U.S. patent application number 11/390793 was filed with the patent office on 2006-12-21 for protein-resistant articles comprising cyclobutanediol.
Invention is credited to Gary Wayne Connell, Emmett Dudley Crawford, David Scott Porter.
Application Number | 20060286389 11/390793 |
Document ID | / |
Family ID | 36630440 |
Filed Date | 2006-12-21 |
United States Patent
Application |
20060286389 |
Kind Code |
A1 |
Crawford; Emmett Dudley ; et
al. |
December 21, 2006 |
Protein-resistant articles comprising cyclobutanediol
Abstract
This invention relates to a medical device comprising a UV-cured
silicone polymer coating on at least a portion of a surface of the
device and at least one polyester composition comprising a
cyclobutanediol and methods for making the medical device.
Inventors: |
Crawford; Emmett Dudley;
(Kingsport, TN) ; Porter; David Scott;
(Blountville, TN) ; Connell; Gary Wayne; (Church
Hill, TN) |
Correspondence
Address: |
Louis N. Moreno;Eastman Chemical Company
P.O. Box 511
Kingsport
TN
37662-5075
US
|
Family ID: |
36630440 |
Appl. No.: |
11/390793 |
Filed: |
March 28, 2006 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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60691567 |
Jun 17, 2005 |
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60731454 |
Oct 28, 2005 |
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60731389 |
Oct 28, 2005 |
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60739058 |
Nov 22, 2005 |
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60738869 |
Nov 22, 2005 |
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60750692 |
Dec 15, 2005 |
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60750693 |
Dec 15, 2005 |
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60750682 |
Dec 15, 2005 |
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60750547 |
Dec 15, 2005 |
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Current U.S.
Class: |
428/447 |
Current CPC
Class: |
C08J 7/123 20130101;
B29K 2067/00 20130101; C08J 2367/02 20130101; Y10T 428/139
20150115; C08J 2367/00 20130101; B32B 27/36 20130101; B01D 61/30
20130101; Y10T 428/31507 20150401; C08K 5/521 20130101; B29L
2031/7542 20130101; A61M 1/16 20130101; C08J 7/0427 20200101; Y10T
428/1397 20150115; B65D 1/0207 20130101; C08L 69/00 20130101; B29B
2911/14986 20130101; B29C 49/00 20130101; C08K 3/32 20130101; Y02A
40/25 20180101; C09D 167/02 20130101; E04D 13/03 20130101; G02B
1/14 20150115; A01G 9/1438 20130101; Y10T 428/24942 20150115; Y10T
428/1352 20150115; C08G 63/183 20130101; B65D 43/00 20130101; C08L
101/00 20130101; A47F 5/00 20130101; B65D 25/00 20130101; C08J 5/18
20130101; Y10T 428/24107 20150115; C08K 2201/014 20130101; E01F
8/0005 20130101; B32B 17/10018 20130101; B65D 23/10 20130101; C08G
63/199 20130101; Y10T 428/24479 20150115; C08J 2483/00 20130101;
G02F 1/133606 20130101; Y10T 428/31504 20150401; Y10T 428/161
20150115; C08L 67/02 20130101; Y10T 428/162 20150115; G02B 1/105
20130101; Y10T 428/31663 20150401; G02B 1/10 20130101; Y10T
428/31786 20150401; G02B 5/3083 20130101; C08L 67/02 20130101; C08L
2666/02 20130101; C08L 67/02 20130101; C08L 2666/18 20130101; C08L
69/00 20130101; C08L 2666/18 20130101; C08K 3/32 20130101; C08L
67/00 20130101; C08K 5/521 20130101; C08L 67/02 20130101 |
Class at
Publication: |
428/447 |
International
Class: |
B32B 9/04 20060101
B32B009/04 |
Claims
1. A medical device comprising: (1) a UV-cured silicone polymer
coating on at least a portion of a surface of the device; and (2)
at least one polyester composition comprising at least one
polyester which comprises: (a) a dicarboxylic acid component
comprising: i) 70 to 100 mole % of terephthalic acid residues; ii)
0 to 30 mole % of aromatic dicarboxylic acid residues having up to
20 carbon atoms; and iii) 0 to 10 mole % of aliphatic dicarboxylic
acid residues having up to 16 carbon atoms; and (b) a glycol
component comprising: i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and ii) 1 to 99
mole % of 1,4-cyclohexanedimethanol residues, wherein the total
mole % of the dicarboxylic acid component is 100 mole %, and the
total mole % of the glycol component is 100 mole %; and wherein the
inherent viscosity of the polyester is from 0.10 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of from 85 to 200.degree. C.
2. A medical device comprising: (1) a UV-cured silicone polymer
coating on at least a portion of a surface of the device; and (2)
at least one polyester composition comprising at least one
polyester which comprises: (a) a dicarboxylic acid component
comprising: i) 70 to 100 mole % of terephthalic acid residues; ii)
0 to 30 mole % of aromatic dicarboxylic acid residues having up to
20 carbon atoms; and iii) 0 to 10 mole % of aliphatic dicarboxylic
acid residues having up to 16 carbon atoms; and (b) a glycol
component comprising: i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and ii) 35 to 60
mole % of 1,4-cyclohexanedimethanol residues, wherein the total
mole % of the dicarboxylic acid component is 100 mole %, and the
total mole % of the glycol component is 100 mole %; and wherein the
inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 85 to 200.degree. C.
3. A medical device comprising: (1) a UV-cured silicone polymer
coating on at least a portion of a surface of the device; and (2)
at least one polyester composition comprising at least one
polyester which comprises: (a) a dicarboxylic acid component
comprising: i) 70 to 100 mole % of terephthalic acid residues; ii)
0 to 30 mole % of aromatic dicarboxylic acid residues having up to
20 carbon atoms; and iii) 0 to 10 mole % of aliphatic dicarboxylic
acid residues having up to 16 carbon atoms; and (b) a glycol
component comprising: i) 40 to 80 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and ii) 20 to 60
mole % of 1,4-cyclohexanedimethanol residues, wherein the total
mole % of the dicarboxylic acid component is 100 mole %, and the
total mole % of the glycol component is 100 mole %; and wherein the
inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 125 to 200.degree. C.
4. A medical device comprising: (1) a UV-cured silicone polymer
coating on at least a portion of a surface of the device; and (2)
at least one polyester which comprises (a) a dicarboxylic acid
component comprising: i) from 70 to 100 mole % of terephthalic acid
residues; ii) 0 to 30 mole % of aromatic dicarboxylic acid residues
having up to 20 carbon atoms; and iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and (b) a
glycol component comprising: i) 15 to 70 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and ii) 30 to 85
mole % of 1,4-cyclohexanedimethanol residues, wherein the total
mole % of the dicarboxylic acid component is 100 mole %, and the
total mole % of the glycol component is 100 mole %; and wherein the
inherent viscosity of the polyester is from 0.5 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.
5. The device of claim 1, wherein the coating comprises an
epoxy-functional polysiloxane and a UV curing agent.
6. The device of claim 1, further comprising a patterned surface
defined by the coating.
7. The device of claim 1, wherein at least a portion of the surface
of device is protein resistant.
8. The device of claim 1, wherein said polyester has a Tg of 110 to
200.degree. C.
9. The device of claims 1, wherein said polyester has a Tg of 110
to 170.degree. C.
10. The device of claim 1, wherein said polyester has a Tg of 110
to 160.degree. C.
11. The device of claim 1, wherein said polyester has a Tg of 110
to 150.degree. C.
12. The device of claim 1, wherein said polyester has a Tg of 110
to 130.degree. C.
13. The device of claim 1, wherein said polyester has a Tg of 120
to 160.degree. C.
14. The device of claim 1, wherein said polyester has a Tg of 120
to 150.degree. C.
15. The device of claim 1, wherein said polyester has a Tg of 130
to 160.degree. C.
16. The device of claim 1, wherein said polyester has a Tg of 130
to 150.degree. C.
17. The device of claim 1, wherein said polyester has a Tg of 130
to 145.degree. C.
18. The device of claim 1, wherein said polyester has a Tg of 140
to 150.degree. C.
19. The device of claim 1, wherein said polyester has a Tg of 135
to 145.degree. C.
20. The device of claim 1, wherein the glycol component of said
polyester comprises 40 to 64.9 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35.1 to 60 mole %
1,4-cyclohexanedimethanol.
21. The device of claim 1, wherein the glycol component of said
polyester comprises 40 to 55 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 60 mole %
1,4-cyclohexanedimethanol.
22. The device of claim 1, wherein the glycol component of said
polyester comprises 45 to 60 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 40 to 55 mole %
1,4-cyclohexanedimethanol.
23. The device of claim 1, wherein the glycol component of said
polyester comprises 45 to 55 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 55 mole %
1,4-cyclohexanedimethanol.
24. The device of claim 1, wherein the glycol component of said
polyester comprises 46 to 55 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to less than 55 mole
% 1,4-cyclohexanedimethanol.
25. The device of claim 1, wherein the glycol component of said
polyester comprises 46 to 55 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to less than 55 mole
% 1,4-cyclohexanedimethanol.
26. The device of claim 1, wherein the dicarboxylic acid component
comprises 80 to 100 mole % of terephthalic acid, an ester thereof,
or a mixture thereof.
27. The device of claim 1, wherein the dicarboxylic acid component
comprises 90 to 100 mole % of terephthalic acid, an ester thereof,
or a mixture thereof.
28. The device of claim 1, wherein the dicarboxylic acid component
comprises 95 to 100 mole % of terephthalic acid, an ester thereof,
or a mixture thereof.
29. The device of claim 1, wherein said polyester comprises
1,3-propanediol, 1,4-butanediol, or mixtures thereof.
30. The device of claim 1, wherein said polyester comprises less
than 15 mole % of residues from at least one modifying glycol.
31. The device of claim 1, wherein said polyester comprises less
than 15 mole % of ethylene glycol residues.
32. The device of claim 1, wherein said polyester comprises
2,2,4,4-tetramethyl-1,3-cyclobutanediol in the pure cis form, the
pure trans form, or mixtures of the cis and trans forms.
33. The device of claim 1, wherein said
2,2,4,4-tetramethyl-1,3-cyclobutanediol is a mixture comprising
greater than 50 mole % of
cis-2,2,4,4-tetramethyl-1,3-cyclobutanediol and less than 50 mole %
of trans-2,2,4,4-tetramethyl-1,3-cyclobutanediol.
34. The device of claim 1, wherein said
2,2,4,4-tetramethyl-1,3-cyclobutanediol is a mixture comprising
greater than 55 mole % of
cis-2,2,4,4-tetramethyl-1,3-cyclobutanediol and less than 45 mole %
of trans-2,2,4,4-tetramethyl-1,3-cyclobutanediol.
35. The device of claim 1, wherein said
2,2,4,4-tetramethyl-1,3-cyclobutanediol is a mixture comprising
greater than 70 mole % of
cis-2,2,4,4-tetramethyl-1,3-cyclobutanediol and less than 30 mole %
of trans-2,2,4,4-tetramethyl-1,3-cyclobutanediol.
36. The device of claim 1, wherein said
2,2,4,4-tetramethyl-1,3-cyclobutanediol is a mixture comprising 30
to 70 mole % of trans-2,2,4,4-tetramethyl-1,3-cyclobutanediol and
30 to 70 mole % of cis-2,2,4,4-tetramethyl-1,3-cyclobutanediol.
37. The device of claim 1, wherein said
2,2,4,4-tetramethyl-1,3-cyclobutanediol is a mixture comprising 50
to 70 mole % of trans-2,2,4,4-tetramethyl-1,3-cyclobutanediol and
30 to 50 mole % of cis-2,2,4,4-tetramethyl-1,3-cyclobutanediol.
38. The device of claim 1, wherein said polyester composition
comprises at least one polymer chosen from poly(amides),
poly(etherimides), polyphenylene oxides, poly(phenylene
oxide)/polystyrene blends, polystyrene resins, polyphenylene
sulfides, polyphenylene sulfide/sulfones, poly(ester-carbonates),
polycarbonates, polysulfones; polysulfone ethers, and
poly(ether-ketones).
39. The device of claim 1, wherein said polyester comprises a
branching agent for the polyester.
40. The device of claim 1, wherein said polyester is linear.
41. The device of claim 1, wherein said polyester composition
comprises at least one polycarbonate.
42. The device of claim 1, wherein said polyester comprises a
branching agent for the polycarbonate.
43. The device of claim 1, wherein said polyester comprises a
branching agent in an amount of 0.01 to 10 weight % based on the
total weight of the polyester.
44. The device of claim 1, wherein said polyester comprises a
branching agent in an amount of 0.01 to 5 weight % based on the
total weight of the polyester.
45. The device of claim 1, wherein the melt viscosity of said
polyester is less than 30,000 poise as measured at 1 radian/second
on a rotary melt rheometer at 290.degree. C.
46. The device of claim 1, wherein the melt viscosity of said
polyester is less than 20,000 poise as measured at 1 radian/second
on a rotary melt rheometer at 290.degree. C.
47. The device of claim 1, wherein said polyester has a
crystallization half-time greater than 5 minutes at 170.degree.
C.
48. The device of claim 1, wherein said polyester has a
crystallization half-time of greater than 1,000 minutes at
170.degree. C.
49. The device of claim 1, wherein said polyester has a
crystallization half-time of greater than 10,000 minutes at
170.degree. C.
50. The device of claim 1, wherein said polyester composition has a
density of less than 1.2 g/ml at 23.degree. C.
51. The device of claim 1, wherein said polyester composition has a
density of less than 1.18 g/ml at 23.degree. C.
52. The device of claim 1, wherein said polyester composition
comprises at least one thermal stabilizer or reaction products
thereof.
53. The device of claim 1, wherein the yellowness index of said
polyester according to ASTM D-1925 is less than 50.
54. The device of claim 1, wherein the b* value of said polyester
is from 0 to less than 10.
55. The device of claim 1, wherein the L* value of said polyester
is from 50 to 90.
56. The device of claim 1, wherein the b* value of said polyester
is from 0 to less than 10 and the L* value of said polyester is
from 50 to 90.
57. The device of claim 1, wherein said polyester has a notched
Izod impact strength of at least 3 ft-lbs/in at 23.degree. C.
according to ASTM D256 with a 10-mil notch in a 1/8-inch thick
bar.
58. The device of claim 1, wherein said polyester has a notched
Izod impact strength of at least 10 ft-lbs/in at 23.degree. C.
according to ASTM D256 with a 10-mil notch in a 1/8-inch thick
bar.
59. The device of claim 1, wherein the polyester comprises at least
one catalyst comprising a tin compound or a reaction product
thereof and/or residues thereof.
60. The device of claim 1, wherein the polyester comprises at least
one chain extender.
61. The device of claim 1, wherein the polyester comprises an
additive chosen from at least one of the following: colorants,
dyes, mold release agents, flame retardants, plasticizers,
nucleating agents, UV stabilizers, thermal stabilizers and/or
reaction products thereof, fillers, and impact modifiers.
62. A method for reducing interaction between the medical device of
claim 1 and a biological fluid or system, said method comprising:
coating at least a portion of a surface of the device with a
UV-curable silicone polymer composition; and exposing at least a
portion of said UV-curable silicone polymer composition to
ultraviolet light to cure the composition.
63. The method of claim 62, wherein the silicone polymer
composition comprises an epoxy-functional polysiloxane and a UV
curing agent.
64. The method of claim 63, further comprising: removing any
uncured silicone polymer composition from the surface of the device
to produce a patterned surface comprising areas of relatively low
protein binding and relatively high protein binding.
65. The method of claim 64, wherein the curing time is 5 seconds or
less.
Description
CROSS-REFERENCE TO RELATED APPLICATION
[0001] This application claims priority under 35 U.S.C. .sctn.
119(e) to U.S. Provisional Patent Application No. 60/642,622, filed
on Jan. 10, 2005, U.S. Provisional Application Ser. No. 60/691,567
filed on Jun. 17, 2005, U.S. Provisional Application Ser. No.
60/731,454 filed on Oct. 28, 2005, U.S. Provisional Application
Ser. No. 60/731,389, filed on Oct. 28, 2005, U.S. Provisional
Application Ser. No. 60/739,058, filed on Nov. 22, 2005, and U.S.
Provisional Application Ser. No. 60/738,869, filed on Nov. 22,
2005, U.S. Provisional Application Ser. No. 60/750,692 filed on
Dec. 15, 2005, U.S. Provisional Application Ser. No. 60/750,693,
filed on Dec. 15, 2005, U.S. Provisional Application Ser. No.
60/750,682, filed on Dec. 15, 2005, and U.S. Provisional
Application Ser. No. 60/750,547, filed on Dec. 15, 2005, all of
which are hereby incorporated by this reference in their
entireties.
FIELD OF THE INVENTION
[0002] The invention generally relates to protein-resistant
articles, including medical devices, comprising a polyester
comprising a cyclobutanediol. More particularly the present
invention generally relates to protein resistant articles,
including medical devices, comprising a UV-cured silicone polymer
coating composition and a polyester made from terephthalic acid or
an ester thereof, or mixtures thereof,
2,2,4,4-tetramethyl-1,3-cyclobutanediol, and
1,4-cyclohexanedimethanol, the polyester having a certain
combination of inherent viscosity and glass transition temperature
(Tg). These medical devices are believed to have a unique
combination of at least one of high impact strengths, high glass
transition temperature (T.sub.g), low ductile-to-brittle transition
temperatures, good color and clarity, low densities, and long
crystallization half-times, which allow them to be easily formed
into articles. The invention also relates to a method for reducing
interaction between the cyclobutanediol containing, protein
resistant articles and a biological fluid or system.
BACKGROUND OF THE INVENTION
[0003] This invention pertains to the improvement of protein
resistance and biocompatibility of articles that come into contact
with biological systems, through the application of biocompatible
coatings. These coatings have uses in many different areas in which
the adsorption of proteins may be problematic, such as diagnostic
tests in which quantification of the amount of proteins in a sample
may be complicated by adsorption of proteins at the surface of a
medical device, as well as operations in which the buildup of
proteins can prevent proper operation, such as filtration
apparatus. Additionally, the importance of biocompatible articles
arises in part from their utility in medical devices. The term
"medical device," as used herein, describes an apparatus that is
used in the diagnosis or treatment of a disease and that come into
contact with biological materials, including tissue, blood, or
other biological fluids, from animals, humans or plants. The term
`biocompatible` is used herein to describe the effect of
substantially reducing by greater than about 50%, preferably
greater than about 80%, more preferably by greater than about 90%
or minimizing or eliminating completely the interaction between a
biological system and the introduced foreign surface. The term
"protein-resistant" is used herein to describe a reduced tendency
to adsorb protein compared to an uncoated surface or article.
[0004] Though a material used for a particular application might
have low reactivity, low levels of extractable substances, and/or
be otherwise inert, biological systems may have adverse reactions
to the introduction of such a foreign surface. This is due to the
interaction of proteins with the foreign surface. It is accepted
that the first observable event to occur when a foreign surface
contacts a biological system is the adsorption of proteins, and
this adsorption can dictate the type and extent of the response to
that surface. (J. D. Andrade and V. Hlady, Protein Adsorption and
Materials Biocompatibility: A Tutorial Review and Suggested
Hypotheses, in Advances in Polymer Science, 79, (1986), p. 3; L.
Vroman and A. L. Adams, Journal of Biomedical Materials Research,
3, (1969), p. 43.)
[0005] One approach to overcoming any negative effects associated
with the contact of a surface with a biological system is to form
the entire article out of a biocompatible material. While several
materials have been identified as biocompatible, these materials
may not possess all of the other necessary properties to be
successfully employed. The particular needs of an application may
dictate that a particular article be formed of materials with
specific characteristics, examples of which are physical properties
such as stiffness or optical clarity.
[0006] Poly(1,4-cyclohexylenedimethylene)terephthalate (PCT), a
polyester based solely on terephthalic acid and
1,4-cyclohexanedimethanol, is known in the art and is commercially
available. This polyester crystallizes rapidly upon cooling from
the melt, making it very difficult to form amorphous articles by
methods known in the art such as extrusion, injection molding, and
the like. In order to slow down the crystallization rate of PCT,
copolyesters can be prepared containing additional dicarboxylic
acids or glycols such as isophthalic acid or ethylene glycol. These
ethylene glycol- or isophthalic acid-modified PCTs are also known
in the art and are commercially available.
[0007] One common copolyester used to produce films, sheeting, and
molded articles is made from terephthalic acid,
1,4-cyclohexanedimethanol, and ethylene glycol. While these
copolyesters are useful in many end-use applications, they exhibit
deficiencies in properties such as glass transition temperature and
impact strength when sufficient modifying ethylene glycol is
included in the formulation to provide for long crystallization
half-times. For example, copolyesters made from terephthalic acid,
1,4-cyclohexanedimethanol, and ethylene glycol with sufficiently
long crystallization half-times to provide for amorphous products
exhibiting higher ductile-to-brittle transition temperatures and
lower glass transition temperatures than the compositions revealed
herein.
[0008] The polycarbonate of 4,4'-isopropylidenediphenol (bisphenol
A polycarbonate) has been used as an alternative for polyesters
known in the art and is a well known engineering molding plastic.
Bisphenol A polycarbonate is a clear, high-performance plastic
having good physical properties such as dimensional stability, high
heat resistance, and good impact strength. Although bisphenol-A
polycarbonate has many good physical properties, its relatively
high melt viscosity leads to poor melt processability and the
polycarbonate exhibits poor chemical resistance. It is also
difficult to thermoform.
[0009] Polymers containing 2,2,4,4-tetramethyl-1,3-cyclobutanediol
have also been generally described in the art. Generally, however,
these polymers exhibit high inherent viscosities, high melt
viscosities and/or high Tgs (glass transition temperatures) such
that the equipment used in industry is insufficient to manufacture
or post polymerization process these materials.
[0010] Thus, there is a need in the art for medical devices
comprising at least one polymer with a unique combination of
properties, such as toughness and high glass transition temperature
of polycarbonate but with the hydrolytic stability, chemical
resistance, lower density and/or thermoformability of polyesters
while retaining processability on the standard equipment used in
the industry.
SUMMARY OF THE INVENTION
[0011] The present inventors have adopted the approach of modifying
the surface of a material having suitable bulk properties to
improve biocompatibility. In particular, the present inventors have
adopted the approach of applying a coated layer of a more
biocompatible material over another material with the appropriate
physical properties. This surface modification is also applied to
polyester compositions comprising a cyclobutanediol.
[0012] The present invention is directed to an ultraviolet light
(UV)-curable, silicone-based coating, on at least a portion of a
surface of a medical device comprising a polyester comprising a
cyclobutanediol, which improves protein resistance and
biocompatibility, may be coated on various substrates, and
overcomes several difficulties identified in previously disclosed
methods.
[0013] It is believed that certain articles, including medical
devices, comprising polyesters made from terephthalic acid, an
ester thereof, or mixtures thereof, 1,4-cyclohexanedimethanol and
2,2,4,4-tetramethyl-1,3-cyclobutanediol with a certain combination
of inherent viscosity and glass transition temperatures are
superior to polyesters known in the art and to polycarbonate with
respect to at least one of hydrolytic stability, toughness,
chemical resistance, lower specific gravity, and thermoformability.
These medical devices are believed to be similar to polycarbonate
in heat resistance and are still processable on the standard
industry equipment.
[0014] In one aspect, the invention provides a protein-resistant
medical device that comprises a UV-cured silicone polymer coating
on at least a portion of the surface thereof.
[0015] In one aspect, this invention relates to a medical device
comprising [0016] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0017] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0018] (a) a dicarboxylic acid component comprising:
[0019] i) 70 to 100 mole % of terephthalic acid residues; [0020]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0021] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0022]
(b) a glycol component comprising: [0023] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0024] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.10 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of from 85 to 200.degree. C.
[0025] In one aspect, this invention relates to a medical device
comprising [0026] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0027] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0028] (a) a dicarboxylic acid component comprising:
[0029] i) 70 to 100 mole % of terephthalic acid residues; [0030]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0031] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0032]
(b) a glycol component comprising: [0033] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0034] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, [0035] (c)
residues of at least one branching agent; wherein the total mole %
of the dicarboxylic acid component is 100 mole %, and the total
mole % of the glycol component is 100 mole %; and wherein the
inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt)phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 85 to 200.degree. C.
[0036] In one aspect, this invention relates to a medical device
comprising [0037] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0038] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0039] (a) a dicarboxylic acid component comprising:
[0040] i) 70 to 100 mole % of terephthalic acid residues; [0041]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0042] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0043]
(b) a glycol component comprising: [0044] i) 1 to 80 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0045] ii) 20
to 99 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 85.degree. C. to 200.degree. C.
[0046] In one aspect, this invention relates to a medical device
comprising [0047] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0048] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0049] (a) a dicarboxylic acid component comprising:
[0050] i) 70 to 100 mole % of terephthalic acid residues; [0051]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0052] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0053]
(b) a glycol component comprising: [0054] i) 40 to 80 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0055] ii) 20
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 125 to 200.degree. C.
[0056] In one aspect, this invention relates to a medical device
comprising [0057] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0058] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0059] (a) a dicarboxylic acid component comprising:
[0060] i) 70 to 100 mole % of terephthalic acid residues; [0061]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0062] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0063]
(b) a glycol component comprising: [0064] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0065] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 85 to 200.degree. C.
[0066] In one aspect, this invention relates to a medical device
comprising [0067] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0068] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0069] (a) a dicarboxylic acid component comprising:
[0070] i) 70 to 100 mole % of terephthalic acid residues; [0071]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0072] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0073]
(b) a glycol component comprising: [0074] i) 40 to 55 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0075] ii) 45
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 85 to 200.degree. C.
[0076] In one aspect, this invention relates to a medical device
comprising [0077] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0078] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0079] (a) a dicarboxylic acid component comprising:
[0080] i) 70 to 100 mole % of terephthalic acid residues; [0081]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0082] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0083]
(b) a glycol component comprising: [0084] i) 40 to 50 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0085] ii) 50
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 85 to 200.degree. C.
[0086] In one aspect, this invention relates to a medical device
comprising [0087] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0088] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0089] (a) a dicarboxylic acid component comprising:
[0090] i) 70 to 100 mole % of terephthalic acid residues; [0091]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0092] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0093]
(b) a glycol component comprising: [0094] i) 45 to 55 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0095] ii) 45
to 55 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 85 to 200.degree. C.
[0096] In one aspect, this invention relates to a medical device
comprising [0097] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0098] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0099] (a) a dicarboxylic acid component comprising:
[0100] i) 70 to 100 mole % of terephthalic acid residues; [0101]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0102] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0103]
(b) a glycol component comprising: [0104] i) greater than 50 up to
99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and
[0105] ii) 1 to less than 50 mole % of 1,4-cyclohexanedimethanol
residues, wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of from 85 to
200.degree. C.
[0106] In one aspect, this invention relates to a medical device
comprising [0107] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0108] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0109] (a) a dicarboxylic acid component comprising:
[0110] i) 70 to 100 mole % of terephthalic acid residues; [0111]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0112] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0113]
(b) a glycol component comprising: [0114] i) greater than 50 up to
80 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and
[0115] ii) 20 to less than 50 mole % of 1,4-cyclohexanedimethanol
residues, wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of from
85.degree. C. to 200.degree. C.
[0116] In one aspect, this invention relates to a medical device
comprising [0117] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0118] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0119] (a) a dicarboxylic acid component comprising:
[0120] i) 70 to 100 mole % of terephthalic acid residues; [0121]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0122] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0123]
(b) a glycol component comprising: [0124] i) greater than 51 up to
80 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and
[0125] ii) 20 to less than 49 mole % of 1,4-cyclohexanedimethanol
residues, wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of from
85.degree. C. to 200.degree. C.
[0126] In one aspect, this invention relates to a medical device
comprising [0127] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0128] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0129] (a) a dicarboxylic acid component comprising:
[0130] i) 70 to 100 mole % of terephthalic acid residues; [0131]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0132] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0133]
(b) a glycol component comprising: [0134] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0135] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, [0136] (c)
residues of at least one branching agent; wherein the total mole %
of the dicarboxylic acid component is 100 mole %, and the total
mole % of the glycol component is 100 mole %; and wherein the
inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt)phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 110 to 300.degree. C.
[0137] In one aspect, this invention relates to a medical device
comprising [0138] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0139] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0140] (a) a dicarboxylic acid component comprising:
[0141] i) 70 to 100 mole % of terephthalic acid residues; [0142]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0143] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0144]
(b) a glycol component comprising: [0145] i) greater than 50 up to
99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and
[0146] ii) 1 to less than 50 mole % of 1,4-cyclohexanedimethanol
residues, wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of from
110.degree. C. to 200.degree. C.
[0147] In one aspect, this invention relates to a medical device
comprising [0148] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0149] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0150] (a) a dicarboxylic acid component comprising:
[0151] i) 70 to 100 mole % of terephthalic acid residues; [0152]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0153] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0154]
(b) a glycol component comprising: [0155] i) greater than 51 up to
99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and
[0156] ii) 1 to less than 49 mole % of 1,4-cyclohexanedimethanol
residues, wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of from
110.degree. C. to 200.degree. C.
[0157] In one aspect, this invention relates to a medical device
comprising [0158] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0159] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0160] (a) a dicarboxylic acid component comprising:
[0161] i) 70 to 100 mole % of terephthalic acid residues; [0162]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0163] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0164]
(b) a glycol component comprising: [0165] i) greater than 50 up to
80 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and
[0166] ii) 20 to less than 50 mole % of 1,4-cyclohexanedimethanol
residues, wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of from
110.degree. C. to 200.degree. C.
[0167] In one aspect, this invention relates to a medical device
comprising [0168] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0169] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0170] (a) a dicarboxylic acid component comprising:
[0171] i) 70 to 100 mole % of terephthalic acid residues; [0172]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0173] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0174]
(b) a glycol component comprising: [0175] i) greater than 51 up to
80 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and
[0176] ii) 20 to less than 49 mole % of 1,4-cyclohexanedimethanol
residues, wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of from
110.degree. C. to 200.degree. C.
[0177] In one aspect, this invention relates to a medical device
comprising [0178] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0179] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0180] (a) a dicarboxylic acid component comprising:
[0181] i) 70 to 100 mole % of terephthalic acid residues; [0182]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0183] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0184]
(b) a glycol component comprising: [0185] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0186] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 0.75 dL/g
as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of from 110 to 300.degree. C.
[0187] In one aspect, this invention relates to a medical device
comprising [0188] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0189] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0190] (a) a dicarboxylic acid component comprising:
[0191] i) 70 to 100 mole % of terephthalic acid residues; [0192]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0193] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0194]
(b) a glycol component comprising: [0195] i) 40 to 80 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0196] ii) 20
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 0.75 dL/g
as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 110 to 300.degree. C.
[0197] In one aspect, this invention relates to a medical device
comprising [0198] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0199] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0200] (a) a dicarboxylic acid component comprising:
[0201] i) 70 to 100 mole % of terephthalic acid residues; [0202]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0203] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0204]
(b) a glycol component comprising: [0205] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0206] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 0.75 dL/g
as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 110 to 300.degree. C.
[0207] In one aspect, this invention relates to a medical device
comprising [0208] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0209] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0210] (a) a dicarboxylic acid component comprising:
[0211] i) 70 to 100 mole % of terephthalic acid residues; [0212]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0213] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0214]
(b) a glycol component comprising: [0215] i) 40 to 55 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0216] ii) 45
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 0.75 dL/g
as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 110 to 300.degree. C.
[0217] In one aspect, this invention relates to a medical device
comprising [0218] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0219] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0220] (a) a dicarboxylic acid component comprising:
[0221] i) 70 to 100 mole % of terephthalic acid residues; [0222]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0223] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0224]
(b) a glycol component comprising: [0225] i) 40 to 50 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0226] ii) 50
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 0.75 dL/g
as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 110 to 300.degree. C.
[0227] In one aspect, this invention relates to a medical device
comprising [0228] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0229] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0230] (a) a dicarboxylic acid component comprising:
[0231] i) 70 to 100 mole % of terephthalic acid residues; [0232]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0233] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0234]
(b) a glycol component comprising: [0235] i) 45 to 55 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0236] ii) 45
to 55 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 0.75 dL/g
as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 110 to 300.degree. C.
[0237] In one aspect, this invention relates to a medical device
comprising [0238] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0239] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0240] (a) a dicarboxylic acid component comprising:
[0241] i) 70 to 100 mole % of terephthalic acid residues; [0242]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0243] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0244]
(b) a glycol component comprising: [0245] i) 40 to 80 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0246] ii) 20
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 0.75 dL/g
as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 110 to 300.degree. C.
[0247] In one aspect, this invention relates to a medical device
comprising [0248] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0249] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0250] (a) a dicarboxylic acid component comprising:
[0251] i) 70 to 100 mole % of terephthalic acid residues; [0252]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0253] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0254]
(b) a glycol component comprising: [0255] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0256] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 and less than
0.70 dL/g as determined in 60/40 (wt/wt) phenol/tetrachloroethane
at a concentration of 0.5 g/100 ml at 25.degree. C.; and wherein
the polyester has a Tg of from 110 to 300.degree. C.
[0257] In one aspect, this invention relates to a medical device
comprising [0258] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0259] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0260] (a) a dicarboxylic acid component comprising:
[0261] i) 70 to 100 mole % of terephthalic acid residues; [0262]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0263] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0264]
(b) a glycol component comprising: [0265] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0266] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is greater than 0.76 up to
1.2 dL/g as determined in 60/40 (wt/wt) phenol/tetrachloroethane at
a concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of from 110.degree. C. to 200.degree. C.
[0267] In one aspect, this invention relates to a medical device
comprising [0268] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0269] (2)
comprising at least one polyester composition comprising at least
one polyester which comprises: [0270] (a) a dicarboxylic acid
component comprising: [0271] i) 70 to 100 mole % of terephthalic
acid residues; [0272] ii) 0 to 30 mole % of aromatic dicarboxylic
acid residues having up to 20 carbon atoms; and [0273] iii) 0 to 10
mole % of aliphatic dicarboxylic acid residues having up to 16
carbon atoms; and [0274] (b) a glycol component comprising: [0275]
i) 40 to 65 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol
residues; and [0276] ii) 35 to 60 mole % of
1,4-cyclohexanedimethanol residues, wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.35 to 1.2 dL/g as determined
in 60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; and wherein the polyester has a Tg of
110 to 150.degree. C.
[0277] In one aspect, this invention relates to a medical device
comprising [0278] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0279] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0280] (a) a dicarboxylic acid component comprising:
[0281] i) 70 to 100 mole % of terephthalic acid residues; [0282]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0283] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0284]
(b) a glycol component comprising: [0285] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0286] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 0.75 dL/g
as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 110 to 150.degree. C.
[0287] In one aspect, this invention relates to a medical device
comprising [0288] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0289] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0290] (a) a dicarboxylic acid component comprising:
[0291] i) 70 to 100 mole % of terephthalic acid residues; [0292]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0293] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0294]
(b) a glycol component comprising: [0295] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0296] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 120 to 135.degree. C.
[0297] In one aspect, this invention relates to a medical device
comprising [0298] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0299] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0300] (a) a dicarboxylic acid component comprising:
[0301] i) 70 to 100 mole % of terephthalic acid residues; [0302]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0303] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0304]
(b) a glycol component comprising: [0305] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0306] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 0.75 dL/g
as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 120 to 135.degree. C.
[0307] In one aspect, this invention relates to a medical device
comprising [0308] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0309] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0310] (a) a dicarboxylic acid component comprising:
[0311] i) 70 to 100 mole % of terephthalic acid residues; [0312]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0313] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0314]
(b) a glycol component comprising: [0315] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0316] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of from 127.degree. C. to 200.degree. C.
[0317] In one aspect, this invention relates to a medical device
comprising [0318] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0319] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0320] (a) a dicarboxylic acid component comprising:
[0321] i) 70 to 100 mole % of terephthalic acid residues; [0322]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0323] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0324]
(b) a glycol component comprising: [0325] i) 1 to 80 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0326] ii) 20
to 99 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 127.degree. C. to 200.degree. C.
[0327] In one aspect, this invention relates to a medical device
comprising [0328] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0329] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0330] (a) a dicarboxylic acid component comprising:
[0331] i) 70 to 100 mole % of terephthalic acid residues; [0332]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0333] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0334]
(b) a glycol component comprising: [0335] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0336] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of from greater than 148.degree. C. up to
200.degree. C.
[0337] In one aspect, this invention relates to a medical device
comprising [0338] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0339] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0340] (a) a dicarboxylic acid component comprising:
[0341] i) 70 to 100 mole % of terephthalic acid residues; [0342]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0343] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0344]
(b) a glycol component comprising: [0345] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0346] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of from greater than 148.degree. C. up to
200.degree. C.
[0347] In one aspect, this invention relates to a medical device
comprising [0348] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0349] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0350] (a) a dicarboxylic acid component comprising:
[0351] i) 70 to 100 mole % of terephthalic acid residues; [0352]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0353] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0354]
(b) a glycol component comprising: [0355] i) 40 to 64.9 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0356] ii) 35
to 59.9 mole % of 1,4-cyclohexanedimethanol residues, [0357] iii)
0.10 to less than 15 mole % ethylene glycol residues; wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 85 to 200.degree. C.
[0358] In one aspect, this invention relates to a medical device
comprising [0359] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0360] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0361] (a) a dicarboxylic acid component comprising:
[0362] i) 70 to 100 mole % of terephthalic acid residues; [0363]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0364] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0365]
(b) a glycol component comprising: [0366] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0367] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 85 to 200.degree. C. and optionally, wherein
one or more branching agents is added prior to or during the
polymerization of the polymer.
[0368] In one aspect, this invention relates to a medical device
comprising:
(I) a UV-cured silicone polymer coating on at least a portion of a
surface of the device; and
(II) at least one polyester composition comprising at least one
polyester which comprises:
[0369] (a) a dicarboxylic acid component comprising: [0370] i) 70
to 100 mole % of terephthalic acid residues; [0371] ii) 0 to 30
mole % of aromatic dicarboxylic acid residues having up to 20
carbon atoms; and [0372] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0373]
(b) a glycol component comprising: [0374] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0375] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues; and (III) at
least one thermal stabilizer; wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is 0.35 to 1.2 dL/g as determined in
60/40 (wt/wt)phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; wherein the polyester has a Tg of 85 to
200.degree. C.
[0376] In one aspect, this invention relates to a medical device
comprising
(I) a UV-cured silicone polymer coating on at least a portion of a
surface of the device; and
(II) at least one polyester composition comprising at least one
polyester which comprises:
[0377] (a) a dicarboxylic acid component comprising: [0378] i) 70
to 100 mole % of terephthalic acid residues; [0379] ii) 0 to 30
mole % of aromatic dicarboxylic acid residues having up to 20
carbon atoms; and [0380] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0381]
(b) a glycol component comprising: [0382] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0383] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues; and (III) at
least one thermal stabilizer and/or reaction product(s) thereof;
wherein the total mole % of the dicarboxylic acid component is 100
mole %, and the total mole % of the glycol component is 100 mole %;
and wherein the inherent viscosity of the polyester is 0.35 to 1.2
dL/g as determined in 60/40 (wt/wt)phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 85 to 200.degree. C.
[0384] In one aspect, this invention relates to a medical device
comprising [0385] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0386] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0387] (a) a dicarboxylic acid component comprising:
[0388] i) 70 to 100 mole % of terephthalic acid residues; [0389]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0390] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0391]
(b) a glycol component comprising: [0392] i) 40 to 64.9 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0393] ii) 35
to 59.9 mole % of 1,4-cyclohexanedimethanol residues, [0394] iii)
0.10 to less than 15 mole % ethylene glycol residues; wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.35 to 0.75 dL/g
or less as determined in 60/40 (wt/wt) phenol/tetrachloroethane at
a concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 110 to 300.degree. C.
[0395] In one aspect, this invention relates to a medical device
comprising [0396] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0397] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0398] (a) a dicarboxylic acid component comprising:
[0399] i) 70 to 100 mole % of terephthalic acid residues; [0400]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0401] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0402]
(b) a glycol component comprising: [0403] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0404] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is 0.35 to 0.75 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 110 to 300.degree. C. and optionally, wherein
one or more branching agents is added prior to or during the
polymerization of the polymer.
[0405] In one aspect, this invention relates to a medical device
comprising
(I) a UV-cured silicone polymer coating on at least a portion of a
surface of the device; and
(II) at least one polyester composition comprising at least one
polyester which comprises:
[0406] (a) a dicarboxylic acid component comprising: [0407] i) 70
to 100 mole % of terephthalic acid residues; [0408] ii) 0 to 30
mole % of aromatic dicarboxylic acid residues having up to 20
carbon atoms; and [0409] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0410]
(b) a glycol component comprising: [0411] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0412] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues; (III) at least
one thermal stabilizer; wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is 0.35 to 1.2 dL/g as determined in
60/40 (wt/wt)phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; wherein the polyester has a Tg of 110 to
300.degree. C.
[0413] In one aspect, this invention relates to a medical device
comprising [0414] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0415] (2) at least
one polyester composition comprising: (I) at least one polyester
which comprises: [0416] (a) a dicarboxylic acid component
comprising: [0417] i) 70 to 100 mole % of terephthalic acid
residues; [0418] ii) 0 to 30 mole % of aromatic dicarboxylic acid
residues having up to 20 carbon atoms; and [0419] iii) 0 to 10 mole
% of aliphatic dicarboxylic acid residues having up to 16 carbon
atoms; and [0420] (b) a glycol component comprising: [0421] i) 40
to 65 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;
and [0422] ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol
residues; and (II) at least one thermal stabilizer and/or reaction
products thereof; wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is 0.35 to 1.2 dL/g as determined in 60/40
(wt/wt)phenol/tetrachloroethane at a concentration of 0.5 g/100 ml
at 25.degree. C.; wherein the polyester has a Tg of 110 to
300.degree. C.
[0423] In one aspect, this invention relates to a medical device
comprising [0424] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0425] (2) at least
one polyester composition comprising: (I) at least one polyester
which comprises: [0426] (a) a dicarboxylic acid component
comprising: [0427] i) 70 to 100 mole % of terephthalic acid
residues; [0428] ii) 0 to 30 mole % of aromatic dicarboxylic acid
residues having up to 20 carbon atoms; and [0429] iii) 0 to 10 mole
% of aliphatic dicarboxylic acid residues having up to 16 carbon
atoms; and [0430] (b) a glycol component comprising: [0431] i) 40
to 64.9 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;
and [0432] ii) 35 to 59.9 mole % of 1,4-cyclohexanedimethanol
residues, [0433] iii) 0.10 to less than 15 mole % ethylene glycol
residues; wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.35 to 0.75 dL/g or less as determined in 60/40
(wt/wt) phenol/tetrachloroethane at a concentration of 0.5 g/100 ml
at 25.degree. C.; wherein the polyester has a Tg of 110 to
300.degree. C.
[0434] In one aspect, this invention relates to a medical device
comprising [0435] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0436] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0437] (a) a dicarboxylic acid component comprising:
[0438] i) 70 to 100 mole % of terephthalic acid residues; [0439]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0440] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0441]
(b) a glycol component comprising: [0442] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0443] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is 0.35 to 0.75 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 110 to 300.degree. C. and optionally, wherein
one or more branching agents is added prior to or during the
polymerization of the polymer.
[0444] In one aspect, this invention relates to a medical device
comprising [0445] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0446] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0447] (a) a dicarboxylic acid component comprising:
[0448] i) 70 to 100 mole % of terephthalic acid residues; [0449]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0450] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0451]
(b) a glycol component comprising: [0452] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0453] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, [0454] (c)
residues of at least one branching agent; wherein the total mole %
of the dicarboxylic acid component is 100 mole %, and the total
mole % of the glycol component is 100 mole %; and wherein the
inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt)phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 110 to 300.degree. C.
[0455] In one aspect, this invention relates to a medical device
comprising [0456] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0457] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0458] (a) a dicarboxylic acid component comprising:
[0459] i) 70 to 100 mole % of terephthalic acid residues; [0460]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0461] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0462]
(b) a glycol component comprising: [0463] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0464] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues; and [0465] (c)
at least thermal stabilizer and/or reaction products thereof;
wherein the total mole % of the dicarboxylic acid component is 100
mole %, and the total mole % of the glycol component is 100 mole %;
and wherein the inherent viscosity of the polyester is 0.35 to 1.2
dL/g as determined in 60/40 (wt/wt)phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; wherein the
polyester has a Tg of 110 to 300.degree. C.
[0466] In one aspect, this invention relates to a medical device
comprising [0467] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0468] (2) at least
one polyester composition comprising: (I) at least one polyester
which comprises: [0469] (a) a dicarboxylic acid component
comprising: [0470] i) 70 to 100 mole % of terephthalic acid
residues; [0471] ii) 0 to 30 mole % of aromatic dicarboxylic acid
residues having up to 20 carbon atoms; and [0472] iii) 0 to 10 mole
% of aliphatic dicarboxylic acid residues having up to 16 carbon
atoms; and [0473] (b) a glycol component comprising: [0474] i) 40
to 65 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;
and [0475] ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol
residues; and (II) at least one thermal stabilizer and/or reaction
products thereof; wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is 0.35 to 1.2 dL/g as determined in 60/40
(wt/wt)phenol/tetrachloroethane at a concentration of 0.5 g/100 ml
at 25.degree. C.; wherein the polyester has a Tg of 110 to
300.degree. C.
[0476] In one aspect, this invention relates to a medical device
comprising [0477] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0478] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0479] (a) a dicarboxylic acid component comprising:
[0480] i) 70 to 100 mole % of terephthalic acid residues; [0481]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0482] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0483]
(b) a glycol component comprising: [0484] i) greater than 40 to 99
mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and
[0485] ii) 1 to less than 60 mole % of 1,4-cyclohexanedimethanol
residues; wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.10 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; wherein the polyester has a Tg of 85 to 200.degree.
C.; wherein the polyester is amorphous; wherein if ethylene glycol
residues is present in the glycol component, it is present in less
than 15 mole %.
[0486] In one aspect, this invention relates to a medical device
comprising [0487] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0488] (2) an
amorphous polyester comprising: [0489] (a) a dicarboxylic acid
component comprising: [0490] i) 90 to 100 mole % of terephthalic
acid residues; [0491] ii) up to 10 mole % of aromatic dicarboxylic
acid residues having up to 20 carbon atoms; and [0492] iii) up to
10 mole % of aliphatic dicarboxylic acid residues having up to 16
carbon atoms; and [0493] (b) a glycol component comprising: [0494]
i) from 10 to 100 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol
residues; and [0495] ii) up to 90 mole % of
1,4-cyclohexanedimethanol residues, wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %.
[0496] In one aspect, this invention relates to a medical device
comprising [0497] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0498] (2) an
amorphous polyester comprising: [0499] (a) a dicarboxylic acid
component comprising: [0500] i) 90 to 100 mole % of terephthalic
acid residues; [0501] ii) up to 10 mole % of aromatic dicarboxylic
acid residues having up to 20 carbon atoms; and [0502] iii) up to
10 mole % of aliphatic dicarboxylic acid residues having up to 16
carbon atoms; and [0503] (b) a glycol component comprising: [0504]
i) from 25 to 100 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol
residues; and [0505] ii) up to 75 mole % of
1,4-cyclohexanedimethanol residues, wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the amorphous
polyester has a glass transition temperature (T.sub.g) of greater
than 120.degree. C.
[0506] In one aspect, this invention relates to a medical device
comprising [0507] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0508] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0509] (a) a dicarboxylic acid component comprising:
[0510] i) 70 to 100 mole % of terephthalic acid residues; [0511]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0512] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0513]
(b) a glycol component comprising: [0514] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0515] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is 0.10 to less than 1 dL/g
as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of from 85 to 120.degree. C.
[0516] In one aspect, this invention relates to a medical device
comprising [0517] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0518] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0519] (a) a dicarboxylic acid component comprising:
[0520] i) 70 to 100 mole % of terephthalic acid residues; [0521]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0522] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0523]
(b) a glycol component comprising: [0524] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0525] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of from 85 to 120.degree. C.
[0526] In one aspect, this invention relates to a medical device
comprising [0527] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0528] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0529] (a) a dicarboxylic acid component comprising:
[0530] i) 70 to 100 mole % of terephthalic acid residues; [0531]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0532] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0533]
(b) a glycol component comprising: [0534] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0535] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of from 95.degree. C. to 115.degree. C.
[0536] In one aspect, this invention relates to a medical device
comprising [0537] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0538] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0539] (a) a dicarboxylic acid component comprising:
[0540] i) 70 to 100 mole % of terephthalic acid residues; [0541]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0542] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0543]
(b) a glycol component comprising: [0544] i) 1 to 99 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0545] ii) 1
to 99 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is 0.35 to less than 1 dL/g
as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of from 95.degree. C. to 115.degree. C.
[0546] In one aspect, this invention relates to a medical device
comprising [0547] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0548] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0549] (a) a dicarboxylic acid component comprising:
[0550] i) 70 to 100 mole % of terephthalic acid residues; [0551]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0552] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0553]
(b) a glycol component comprising: [0554] i) 5 to less than 50 mole
% of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0555]
ii) greater than 50 to 95 mole % of 1,4-cyclohexanedimethanol
residues, wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.50 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 85 to
120.degree. C.
[0556] In one aspect, this invention relates to a medical device
comprising [0557] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0558] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0559] (a) a dicarboxylic acid component comprising:
[0560] i) 70 to 100 mole % of terephthalic acid residues; [0561]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0562] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0563]
(b) a glycol component comprising: [0564] i) 10 to 30 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0565] ii) 70
to 90 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.50 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 85 to 120.degree. C.
[0566] In one aspect, this invention relates to a medical device
comprising [0567] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0568] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0569] (a) a dicarboxylic acid component comprising:
[0570] i) 70 to 100 mole % of terephthalic acid residues; [0571]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0572] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0573]
(b) a glycol component comprising: [0574] i) 15 to 25 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0575] ii) 75
to 85 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity is from 0.50 to 1.2 dL/g as determined in
60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; and wherein the polyester has a Tg of 85
to 120.degree. C.
[0576] In one aspect, this invention relates to a medical device
comprising [0577] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0578] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0579] (a) a dicarboxylic acid component comprising:
[0580] i) 70 to 100 mole % of terephthalic acid residues; [0581]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0582] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0583]
(b) a glycol component comprising: [0584] i) 5 to less than 50 mole
% of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0585]
ii) greater than 50 to 95 mole % of 1,4-cyclohexanedimethanol
residues, wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.50 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 95 to
115.degree. C.
[0586] In one aspect, this invention relates to a medical device
comprising [0587] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0588] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0589] (a) a dicarboxylic acid component comprising:
[0590] i) 70 to 100 mole % of terephthalic acid residues; [0591]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0592] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0593]
(b) a glycol component comprising: [0594] i) 10 to 30 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0595] ii)
greater than 70 to 90 mole % of 1,4-cyclohexanedimethanol residues,
wherein the total mole % of the dicarboxylic acid component is 100
mole %, and the total mole % of the glycol component is 100 mole %;
and wherein the inherent viscosity of the polyester is from 0.50 to
1.2 dL/g as determined in 60/40 (wt/wt) phenol/tetrachloroethane at
a concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 95 to 115.degree. C.
[0596] In one aspect, this invention relates to a medical device
comprising [0597] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0598] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0599] (a) a dicarboxylic acid component comprising:
[0600] i) 70 to 100 mole % of terephthalic acid residues; [0601]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0602] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0603]
(b) a glycol component comprising: [0604] i) 15 to 25 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0605] ii)
greater than 75 to 85 mole % of 1,4-cyclohexanedimethanol residues,
wherein the total mole % of the dicarboxylic acid component is 100
mole %, and the total mole % of the glycol component is 100 mole %;
and wherein the inherent viscosity of the polyester is from 0.50 to
1.2 dL/g as determined in 60/40 (wt/wt) phenol/tetrachloroethane at
a concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 95 to 115.degree. C.
[0606] In one aspect, this invention relates to a medical device
comprising [0607] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0608] (2)
comprising at least one polyester composition comprising at least
one polyester which comprises: [0609] (a) a dicarboxylic acid
component comprising: [0610] i) 70 to 100 mole % of terephthalic
acid residues; [0611] ii) 0 to 30 mole % of aromatic dicarboxylic
acid residues having up to 20 carbon atoms; and [0612] iii) 0 to 10
mole % of aliphatic dicarboxylic acid residues having up to 16
carbon atoms; and [0613] (b) a glycol component comprising: [0614]
i) 5 to less than 50 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0615] ii)
greater than 50 to 95 mole % of 1,4-cyclohexanedimethanol residues,
wherein the total mole % of the dicarboxylic acid component is 100
mole %, and the total mole % of the glycol component is 100 mole %;
and wherein the inherent viscosity of the polyester is from 0.50 to
less than 0.75 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 85 to
120.degree. C.
[0616] In one aspect, this invention relates to a medical device
comprising [0617] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0618] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0619] (a) a dicarboxylic acid component comprising:
[0620] i) 70 to 100 mole % of terephthalic acid residues; [0621]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0622] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0623]
(b) a glycol component comprising: [0624] i) 10 to 30 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0625] ii)
greater than 70 to 90 mole % of 1,4-cyclohexanedimethanol residues,
wherein the total mole % of the dicarboxylic acid component is 100
mole %, and the total mole % of the glycol component is 100 mole %;
and wherein the inherent viscosity of the polyester is from 0.50 to
less than 0.75 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 85 to
120.degree. C.
[0626] In one aspect, this invention relates to a medical device
comprising [0627] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0628] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0629] (a) a dicarboxylic acid component comprising:
[0630] i) 70 to 100 mole % of terephthalic acid residues; [0631]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0632] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0633]
(b) a glycol component comprising: [0634] i) 15 to 25 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0635] ii)
greater than 75 to 85 mole % of 1,4-cyclohexanedimethanol residues,
wherein the total mole % of the dicarboxylic acid component is 100
mole %, and the total mole % of the glycol component is 100 mole %;
and wherein the inherent viscosity of the polyester is from 0.50 to
less than 0.75 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 85 to
120.degree. C.
[0636] In one aspect, this invention relates to a medical device
comprising [0637] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0638] (2)
comprising at least one polyester composition comprising at least
one polyester which comprises: [0639] (a) a dicarboxylic acid
component comprising: [0640] i) 70 to 100 mole % of terephthalic
acid residues; [0641] ii) 0 to 30 mole % of aromatic dicarboxylic
acid residues having up to 20 carbon atoms; and [0642] iii) 0 to 10
mole % of aliphatic dicarboxylic acid residues having up to 16
carbon atoms; and [0643] (b) a glycol component comprising: [0644]
i) 5 to less than 50 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0645] ii)
greater than 50 to 95 mole % of 1,4-cyclohexanedimethanol residues,
wherein the total mole % of the dicarboxylic acid component is 100
mole %, and the total mole % of the glycol component is 100 mole %;
and wherein the inherent viscosity of the polyester is from 0.50 to
less than 0.75 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 95 to
115.degree. C.
[0646] In one aspect, this invention relates to a medical device
comprising [0647] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0648] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0649] (a) a dicarboxylic acid component comprising:
[0650] i) 70 to 100 mole % of terephthalic acid residues; [0651]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0652] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0653]
(b) a glycol component comprising: [0654] i) 10 to 30 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0655] ii)
greater than 70 to 90 mole % of 1,4-cyclohexanedimethanol residues,
wherein the total mole % of the dicarboxylic acid component is 100
mole %, and the total mole % of the glycol component is 100 mole %;
and wherein the inherent viscosity of the polyester is from 0.50 to
less than 0.75 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 95 to
115.degree. C.
[0656] In one aspect, this invention relates to a medical device
comprising [0657] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0658] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0659] (a) a dicarboxylic acid component comprising:
[0660] i) 70 to 100 mole % of terephthalic acid residues; [0661]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0662] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0663]
(b) a glycol component comprising: [0664] i) 15 to 25 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0665] ii)
greater than 75 to 85 mole % of 1,4-cyclohexanedimethanol residues,
wherein the total mole % of the dicarboxylic acid component is 100
mole %, and the total mole % of the glycol component is 100 mole %;
and wherein the inherent viscosity of the polyester is from 0.50 to
less than 0.75 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 95 to
115.degree. C.
[0666] In one aspect, this invention relates to a medical device
comprising [0667] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0668] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0669] (a) a dicarboxylic acid component comprising:
[0670] i) 70 to 100 mole % of terephthalic acid residues; [0671]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0672] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0673]
(b) a glycol component comprising: [0674] i) 15 to 25 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0675] ii)
greater than 75 to 85 mole % of 1,4-cyclohexanedimethanol residues,
wherein the total mole % of the dicarboxylic acid component is 100
mole %, and the total mole % of the glycol component is 100 mole %;
and wherein the inherent viscosity of the polyester is from 0.6 to
0.72 dL/g as determined in 60/40 (wt/wt) phenol/tetrachloroethane
at a concentration of 0.5 g/100 ml at 25.degree. C.; and wherein
the polyester has a Tg of 95 to 115.degree. C.
[0676] In one aspect, this invention relates to a medical device
comprising [0677] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0678] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0679] (a) a dicarboxylic acid component comprising:
[0680] i) 70 to 100 mole % of terephthalic acid residues; [0681]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0682] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0683]
(b) a glycol component comprising: [0684] i) 0.01 to less than 5
mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0685]
ii) ethylene glycol residues, and [0686] iii) optionally,
1,4-cyclohexanedimethanol residues wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.35 to 1.2 dL/g as determined
in 60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; and wherein the polyester has a Tg of 60
to 110.degree. C.
[0687] In one aspect, this invention relates to a medical device
comprising [0688] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0689] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0690] (a) a dicarboxylic acid component comprising:
[0691] i) 70 to 100 mole % of terephthalic acid residues; [0692]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0693] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0694]
(b) a glycol component comprising: [0695] i) 0.01 to 4.5 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0696] ii)
ethylene glycol residues, and [0697] iii) optionally,
1,4-cyclohexanedimethanol residues wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.35 to 1.2 dL/g as determined
in 60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; and wherein the polyester has a Tg of 60
to 110.degree. C.
[0698] In one aspect, this invention relates to a medical device
comprising [0699] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0700] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0701] (a) a dicarboxylic acid component comprising:
[0702] i) 70 to 100 mole % of terephthalic acid residues; [0703]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0704] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0705]
(b) a glycol component comprising: [0706] i) 0.01 to 4 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0707] ii)
ethylene glycol residues, and [0708] iii) optionally,
1,4-cyclohexanedimethanol residues wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.35 to 1.2 dL/g as determined
in 60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; and wherein the polyester has a Tg of 60
to 110.degree. C.
[0709] In one aspect, this invention relates to a medical device
comprising [0710] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0711] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0712] (a) a dicarboxylic acid component comprising:
[0713] i) 70 to 100 mole % of terephthalic acid residues; [0714]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0715] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0716]
(b) a glycol component comprising: [0717] i) 0.01 to 3 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0718] ii)
ethylene glycol residues, and [0719] iii) 1,4-cyclohexanedimethanol
residues wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 60 to
110.degree. C.
[0720] In one aspect, this invention relates to a medical device
comprising [0721] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0722] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0723] (a) a dicarboxylic acid component comprising:
[0724] i) 70 to 100 mole % of terephthalic acid residues; [0725]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0726] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0727]
(b) a glycol component comprising: [0728] i) 0.01 to 2.0 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0729] ii)
ethylene glycol residues, and [0730] iii) optionally,
1,4-cyclohexanedimethanol residues wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.35 to 1.2 dL/g as determined
in 60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; and wherein the polyester has a Tg of 60
to 110.degree. C.
[0731] In one aspect, this invention relates to a medical device
comprising [0732] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0733] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0734] (a) a dicarboxylic acid component comprising:
[0735] i) 70 to 100 mole % of terephthalic acid residues; [0736]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0737] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0738]
(b) a glycol component comprising: [0739] i) 0.01 to 1 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0740] ii)
ethylene glycol residues, and [0741] iii) 1,4-cyclohexanedimethanol
residues wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 60 to
110.degree. C.
[0742] In one aspect, this invention relates to a medical device
comprising [0743] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0744] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0745] (a) a dicarboxylic acid component comprising:
[0746] i) 70 to 100 mole % of terephthalic acid residues; [0747]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0748] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0749]
(b) a glycol component comprising: [0750] i) 0.01 to less than 1
mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0751]
ii) ethylene glycol residues, and [0752] iii)
1,4-cyclohexanedimethanol residues wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.35 to 1.2 dL/g as determined
in 60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; and wherein the polyester has a Tg of 60
to 110.degree. C.
[0753] In one aspect, this invention relates to a medical device
comprising [0754] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0755] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0756] (a) a dicarboxylic acid component comprising:
[0757] i) 70 to 100 mole % of terephthalic acid residues; [0758]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0759] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0760]
(b) a glycol component comprising: [0761] i) 0.01 to 15 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0762] ii)
ethylene glycol residues, and [0763] iii) 1,4-cyclohexanedimethanol
residues wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 60 to
110.degree. C.
[0764] In one aspect, this invention relates to a medical device
comprising [0765] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0766] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0767] (a) a dicarboxylic acid component comprising:
[0768] i) 70 to 100 mole % of terephthalic acid residues; [0769]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0770] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0771]
(b) a glycol component comprising: [0772] i) 0.01 to 15 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0773] ii) 70 to
99.08 mole % ethylene glycol residues, and [0774] iii) 0.01 to 15
mole % of 1,4-cyclohexanedimethanol residues wherein the total mole
% of the dicarboxylic acid component is 100 mole %, and the total
mole % of the glycol component is 100 mole %; and wherein the
inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 60 to 110.degree. C.
[0775] In one aspect, this invention relates to a medical device
comprising [0776] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0777] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0778] (a) a dicarboxylic acid component comprising:
[0779] i) 70 to 100 mole % of terephthalic acid residues; [0780]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0781] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0782]
(b) a glycol component comprising: [0783] i) 0.01 to 10 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0784] ii)
ethylene glycol residues, and [0785] iii) 1,4-cyclohexanedimethanol
residues wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 60 to
110.degree. C.
[0786] In one aspect, this invention relates to a medical device
comprising [0787] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0788] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0789] (a) a dicarboxylic acid component comprising:
[0790] i) 70 to 100 mole % of terephthalic acid residues; [0791]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0792] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0793]
(b) a glycol component comprising: [0794] i) 0.01 to 10 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0795] ii) 80 to
99.08 mole % of ethylene glycol residues, and [0796] iii) 0.01 to
10 mole % of 1,4-cyclohexanedimethanol residues wherein the total
mole % of the dicarboxylic acid component is 100 mole %, and the
total mole % of the glycol component is 100 mole %; and wherein the
inherent viscosity of the polyester is from 0.35 to 1.2 dL/g as
determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 60 to 110.degree. C.
[0797] In one aspect, this invention relates to a medical device
comprising [0798] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0799] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0800] (a) a dicarboxylic acid component comprising:
[0801] i) 70 to 100 mole % of terephthalic acid residues; [0802]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0803] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0804]
(b) a glycol component comprising: [0805] i) 0.01 to 5 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0806] ii)
ethylene glycol residues, and [0807] iii) 1,4-cyclohexanedimethanol
residues wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 60 to
110.degree. C.
[0808] In one aspect, this invention relates to a medical device
comprising [0809] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0810] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0811] (a) a dicarboxylic acid component comprising:
[0812] i) 70 to 100 mole % of terephthalic acid residues; [0813]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0814] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0815]
(b) a glycol component comprising: [0816] i) 0.01 to less than 5
mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0817]
ii) ethylene glycol residues, and [0818] iii)
1,4-cyclohexanedimethanol residues wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.35 to 1.2 dL/g as determined
in 60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; and wherein the polyester has a Tg of 60
to 110.degree. C.
[0819] In one aspect, this invention relates to a medical device
comprising [0820] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0821] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0822] (a) a dicarboxylic acid component comprising:
[0823] i) 70 to 100 mole % of terephthalic acid residues; [0824]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0825] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0826]
(b) a glycol component comprising: [0827] i) 0.01 to 4.5 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0828] ii)
ethylene glycol residues, and [0829] iii) 1,4-cyclohexanedimethanol
residues wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 60 to
110.degree. C.
[0830] In one aspect, this invention relates to a medical device
comprising [0831] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0832] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0833] (a) a dicarboxylic acid component comprising:
[0834] i) 70 to 100 mole % of terephthalic acid residues; [0835]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0836] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0837]
(b) a glycol component comprising: [0838] i) 0.01 to 4 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0839] ii)
ethylene glycol residues, and [0840] iii) 1,4-cyclohexanedimethanol
residues wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 60 to
110.degree. C.
[0841] In one aspect, this invention relates to a medical device
comprising [0842] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0843] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0844] (a) a dicarboxylic acid component comprising:
[0845] i) 70 to 100 mole % of terephthalic acid residues; [0846]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0847] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0848]
(b) a glycol component comprising: [0849] i) 0.01 to 3 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0850] ii)
ethylene glycol residues, and [0851] iii) 1,4-cyclohexanedimethanol
residues wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 60 to
110.degree. C.
[0852] In one aspect, this invention relates to a medical device
comprising [0853] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0854] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0855] (a) a dicarboxylic acid component comprising:
[0856] i) 70 to 100 mole % of terephthalic acid residues; [0857]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0858] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0859]
(b) a glycol component comprising: [0860] i) 0.01 to 2.0 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0861] ii)
ethylene glycol residues, and [0862] iii) 1,4-cyclohexanedimethanol
residues wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 85 to
200.degree. C.
[0863] In one aspect, this invention relates to a medical device
comprising [0864] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0865] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0866] (a) a dicarboxylic acid component comprising:
[0867] i) 70 to 100 mole % of terephthalic acid residues; [0868]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0869] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0870]
(b) a glycol component comprising: [0871] i) 0.01 to 1 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0872] ii)
ethylene glycol residues, and [0873] iii) 1,4-cyclohexanedimethanol
residues wherein the total mole % of the dicarboxylic acid
component is 100 mole %, and the total mole % of the glycol
component is 100 mole %; and wherein the inherent viscosity of the
polyester is from 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)
phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at
25.degree. C.; and wherein the polyester has a Tg of 85 to
200.degree. C.
[0874] In one aspect, this invention relates to a medical device
comprising [0875] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0876] (2) at least
one polyester composition comprising at least one polyester which
comprises: [0877] (a) a dicarboxylic acid component comprising:
[0878] i) 70 to 100 mole % of terephthalic acid residues; [0879]
ii) 0 to 30 mole % of aromatic dicarboxylic acid residues having up
to 20 carbon atoms; and [0880] iii) 0 to 10 mole % of aliphatic
dicarboxylic acid residues having up to 16 carbon atoms; and [0881]
(b) a glycol component comprising: [0882] i) 0.01 to less than 1
mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; [0883]
ii) ethylene glycol residues, and [0884] iii)
1,4-cyclohexanedimethanol residues wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.35 to 1.2 dL/g as determined
in 60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; and wherein the polyester has a Tg of 85
to 200.degree. C.
[0885] In one aspect, this invention relates to a medical device
comprising [0886] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0887] (2) at least
one polyester which comprises: [0888] (a) a dicarboxylic acid
component comprising: [0889] i). 70 to 100 mole % of terephthalic
acid residues; [0890] ii) 0 to 30 mole % of aromatic dicarboxylic
acid residues having up to 20 carbon atoms; and [0891] iii) 0 to 10
mole % of aliphatic dicarboxylic acid residues having up to 16
carbon atoms; and [0892] (b) a glycol component comprising: [0893]
i) 40 to 65 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol
residues; and [0894] ii) 35 to 60 mole % of
1,4-cyclohexanedimethanol residues, wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.5 to 0.68 dL/g as determined
in 60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.
[0895] In one aspect, this invention relates to a medical device
comprising [0896] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0897] (2) at least
one polyester which comprises: [0898] (a) a dicarboxylic acid
component comprising: [0899] i) 70 to 100 mole % of terephthalic
acid residues; [0900] ii) 0 to 30 mole % of aromatic dicarboxylic
acid residues having up to 20 carbon atoms; and [0901] iii) 0 to 10
mole % of aliphatic dicarboxylic acid residues having up to 16
carbon atoms; and [0902] (b) a glycol component comprising: [0903]
i) 40 to 65 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol
residues; and [0904] ii) 35 to 60 mole % of
1,4-cyclohexanedimethanol residues, wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; wherein the inherent viscosity
of the polyester is 0.68 dL/g or less as determined in 60/40
(wt/wt) phenol/tetrachloroethane at a concentration of 0.5 g/100 ml
at 25.degree. C.; and optionally, wherein one or more branching
agents is added, but when the branching agent is added, it is added
only prior to or during the polymerization of the polyester.
[0905] In one aspect, this invention relates to a medical device
comprising [0906] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0907] (2) at least
one polyester which comprises: [0908] (a) a dicarboxylic acid
component comprising: [0909] i) from 70 to 100 mole % of
terephthalic acid residues; [0910] ii) 0 to 30 mole % of aromatic
dicarboxylic acid residues having up to 20 carbon atoms; and [0911]
iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues having
up to 16 carbon atoms; and [0912] (b) a glycol component
comprising: [0913] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0914] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, and [0915] (c)
branching agent residues; wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.5 to 1.2 dL/g as determined in
60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C. In one embodiment, the branching agent is
added before or during polymerization of the polymer.
[0916] In one aspect, this invention relates to a medical device
comprising
[0917] (I) a UV-cured silicone polymer coating on at least a
portion of a surface of the device;
[0918] (II) at least one polyester which comprises: [0919] (a) a
dicarboxylic acid component comprising: [0920] i) 70 to 100 mole %
of terephthalic acid residues; [0921] ii) 0 to 30 mole % of
aromatic dicarboxylic acid residues having up to 20 carbon atoms;
and [0922] iii) 0 to 10 mole % of aliphatic dicarboxylic acid
residues having up to 16 carbon atoms; and [0923] (b) a glycol
component comprising: [0924] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0925] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, and
[0926] (III) at least one thermal stabilizer and/or reaction
products thereof;
wherein the total mole % of the dicarboxylic acid component is 100
mole %, and the total mole % of the glycol component is 100 mole %;
and
wherein the inherent viscosity of the polyester is from 0.5 to 1.2
dL/g as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.
[0927] In one aspect, this invention relates to a medical device
comprising [0928] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0929] (2) at least
one polyester which comprises: [0930] (a) a dicarboxylic acid
component comprising: [0931] i) from 70 to 100 mole % of
terephthalic acid residues; [0932] ii) 0 to 30 mole % of aromatic
dicarboxylic acid residues having up to 20 carbon atoms; and [0933]
iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues having
up to 16 carbon atoms; and [0934] (b) a glycol component
comprising: [0935] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol; and [0936] ii) 35 to 60
mole % of 1,4-cyclohexanedimethanol, wherein the total mole % of
the dicarboxylic acid component is 100 mole %, and the total mole %
of the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.50 to 1.2 dL/g as determined
in 60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; and wherein the polyester has a Tg of
110 to 160.degree. C. or 110 to 150.degree. C. or 120 to
160.degree. C. or 120 to 150.degree. C. or 120 to 135.degree. C. or
130 to 145.degree. C., as well as other glass transition
temperatures (Tgs) described herein, as measured by a TA DSC 2920
from Thermal Analyst Instrument at a scan rate of 20.degree.
C./min.
[0937] In one aspect, this invention relates to a medical device
comprising [0938] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0939] (2) at least
one polyester which comprises: [0940] (a) a dicarboxylic acid
component comprising: [0941] i) 70 to 100 mole % of terephthalic
acid residues; [0942] ii) 0 to 30 mole % of aromatic dicarboxylic
acid residues having up to 20 carbon atoms; and [0943] iii) 0 to 10
mole % of aliphatic dicarboxylic acid residues having up to 16
carbon atoms; and [0944] (b) a glycol component comprising: [0945]
i) 40 to 65 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol; and
[0946] ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol, wherein
the total mole % of the dicarboxylic acid component is 100 mole %,
and the total mole % of the glycol component is 100 mole %; and
wherein the inherent viscosity of the polyester is from 0.50 to
0.75 dL/g as determined in 60/40 (wt/wt) phenol/tetrachloroethane
at a concentration of 0.5 g/100 ml at 25.degree. C.; and wherein
the polyester has a Tg of 110 to 160.degree. C. or 110 to
150.degree. C. or 120 to 160.degree. C. or 120 to 150.degree. C. or
120 to 135.degree. C. or 130 to 145.degree. C., as measured by a TA
DSC 2920 from Thermal Analyst Instrument at a scan rate of
20.degree. C./min.
[0947] In one aspect, this invention relates to a medical device
comprising [0948] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0949] (2) at least
one polyester which comprises: [0950] (a) a dicarboxylic acid
component comprising: [0951] i) from 70 to 100 mole % of
terephthalic acid residues; [0952] ii) 0 to 30 mole % of aromatic
dicarboxylic acid residues having up to 20 carbon atoms; and [0953]
iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues having
up to 16 carbon atoms; and [0954] (b) a glycol component
comprising: [0955] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0956] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.50 to 0.72 dL/g
as determined in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C.; and wherein the
polyester has a Tg of 110 to 160.degree. C. or 110 to 150.degree.
C. or 120 to 160.degree. C. or 120 to 150.degree. C. or 120 to
135.degree. C. or 130 to 145.degree. C., as measured by a TA DSC
2920 from Thermal Analyst Instrument at a scan rate of 20.degree.
C./min.
[0957] In one aspect, this invention relates to a medical device
comprising [0958] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0959] (2) at least
one polyester which comprises: [0960] (a) a dicarboxylic acid
component comprising: [0961] i) 70 to 100 mole % of terephthalic
acid residues; [0962] ii) 0 to 30 mole % of aromatic dicarboxylic
acid residues having up to 20 carbon atoms; and [0963] iii) 0 to 10
mole % of aliphatic dicarboxylic acid residues having up to 16
carbon atoms; and [0964] (b) a glycol component comprising: [0965]
i) 40 to 65 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol
residues; and [0966] ii) 35 to 60 mole % of
1,4-cyclohexanedimethanol residues, wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.50 to 0.68 dL/g as determined
in 60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; and wherein the polyester has a Tg of
110 to 160.degree. C. or 110 to 150.degree. C. or 120 to
160.degree. C. or 120 to 150.degree. C. or 120 to 135.degree. C. or
130 to 145.degree. C., as measured by a TA DSC 2920 from Thermal
Analyst Instrument at a scan rate of 20.degree. C./min.
[0967] In one aspect, this invention relates to a medical device
comprising [0968] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0969] (2) at least
one polyester which comprises: [0970] (a) a dicarboxylic acid
component comprising: [0971] i) from 70 to 100 mole % of
terephthalic acid residues; [0972] ii) 0 to 30 mole % of aromatic
dicarboxylic acid residues having up to 20 carbon atoms; and [0973]
iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues having
up to 16 carbon atoms; and [0974] (b) a glycol component
comprising: [0975] i) 40 to 65 mole % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and [0976] ii) 35
to 60 mole % of 1,4-cyclohexanedimethanol residues, wherein the
total mole % of the dicarboxylic acid component is 100 mole %, and
the total mole % of the glycol component is 100 mole %; and wherein
the inherent viscosity of the polyester is from 0.50 to less than
0.68 dL/g as determined in 60/40 (wt/wt) phenol/tetrachloroethane
at a concentration of 0.5 g/100 ml at 25.degree. C.; and wherein
the polyester has a Tg of 110 to 160.degree. C. or 110 to
150.degree. C. or 120 to 160.degree. C. or 120 to 150.degree. C. or
120 to 135.degree. C. or 130 to 145.degree. C., as measured by a TA
DSC 2920 from Thermal Analyst Instrument at a scan rate of
20.degree. C./min.
[0977] In one aspect, this invention relates to a medical device
comprising [0978] (1) a UV-cured silicone polymer coating on at
least a portion of a surface of the device; and [0979] (2) at least
one polyester which comprises: [0980] (a) a dicarboxylic acid
component comprising: [0981] i) 70 to 100 mole % of terephthalic
acid residues; [0982] ii) 0 to 30 mole % of aromatic dicarboxylic
acid residues having up to 20 carbon atoms; and [0983] iii) 0 to 10
mole % of aliphatic dicarboxylic acid residues having up to 16
carbon atoms; and [0984] (b) a glycol component comprising: [0985]
i) 40 to 65 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol
residues; and [0986] ii) 35 to 60 mole % of
1,4-cyclohexanedimethanol residues, wherein the total mole % of the
dicarboxylic acid component is 100 mole %, and the total mole % of
the glycol component is 100 mole %; and wherein the inherent
viscosity of the polyester is from 0.50 to 1.2 dL/g as determined
in 60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.; and wherein the polyester has a Tg of
120 to 135.degree. C. as measured by a TA DSC 2920 from Thermal
Analyst Instrument at a scan rate of 20.degree. C./min.
[0987] In one aspect, the polyesters useful in the invention
contain less than 15 mole % ethylene glycol residues, such as, for
example, 0.01 to less than 15 mole % ethylene glycol residues.
[0988] In one aspect, the polyesters useful in the invention
contain no ethylene glycol residues.
[0989] In one aspect the polyester compositions useful in the
invention contain at least one thermal stabilizer and/or reaction
products thereof.
[0990] In one aspect, the polyesters useful in the invention
contain no branching agent, or alternatively, at least one
branching agent is added either prior to or during polymerization
of the polyester.
[0991] In one aspect, the polyesters useful in the invention
contain at least one branching agent without regard to the method
or sequence in which it is added.
[0992] In one aspect, the polyesters useful in the invention are
made from no 1,3-propanediol, or, 1,4-butanediol, either singly or
in combination. In other aspects, 1,3-propanediol or
1,4-butanediol, either singly or in combination, may be used in the
making of the polyester of this invention.
[0993] In one aspect of the invention, the mole % of
cis-2,2,4,4-tetramethyl-1,3-cyclobutanediol is greater than 50 mole
% or greater than 55 mole % of
cis-2,2,4,4-tetramethyl-1,3-cyclobutanediol or greater than 70 mole
% of cis-2,2,4,4-tetramethyl-1,3-cyclobutanediol; wherein the total
mole percentage of cis-2,2,4,4-tetramethyl-1,3-cyclobutanediol and
trans-2,2,4,4-tetramethyl-1,3-cyclobutanediol is equal to a total
of 100 mole %.
[0994] In one aspect, the polyester compositions are useful in
articles of manufacture, such as medical devices, including but not
limited to, extruded, calendered, and/or molded articles including
but not limited to, injection molded articles, extruded articles,
cast extrusion articles, profile extrusion articles, melt spun
articles, extrusion molded articles, injection blow molded
articles, injection stretch blow molded articles and extrusion blow
molded articles. These articles can include, but are not limited
to, films, bottles, containers, sheet and/or fibers.
[0995] In one aspect, the polyester compositions useful in the
invention may be used in various types of film and/or sheet,
including but not limited to extruded film(s) and/or sheet(s),
calendered film(s) and/or sheet(s), compression molded film(s)
and/or sheet(s), solution casted film(s) and/or sheet(s). Methods
of making film and/or sheet include but are not limited to
extrusion, calendering, compression molding, and solution
casting.
[0996] Also, in one aspect, use of these particular polyester
compositions minimizes and/or eliminates the drying step prior to
melt processing and/or thermoforming.
[0997] In one aspect, the polyester compositions are useful in
medical devices including but not limited to extruded and/or molded
articles including but not limited to injection molded articles,
extrusion molded articles, injection blow molded articles,
injection stretch blow molded articles, extrusion blow molded
articles and extrusion stretch blow molded articles. These medical
devices can include but are not limited to bottles.
[0998] In one aspect, the polyesters useful in the medical devices
of the invention may be amorphous or semicrystalline. In one
aspect, certain polyesters useful in the invention can have a
relatively low crystallinity. Certain polyesters useful in the
invention can thus have a substantially amorphous morphology,
meaning that the polyesters comprise substantially unordered
regions of polymer.
[0999] In another aspect, the invention provides a method for
reducing interaction between a medical device and a biological
fluid or system. The method comprises coating at least a portion of
a surface of the device with a UV-curable silicone polymer
composition and exposing at least a portion of the silicone polymer
composition to ultraviolet light to cure the composition.
[1000] The use of a UV-curable silicone polymer coating composition
allows for rapid curing, low-temperature curing for
temperature-sensitive substrates, as well as patterning of the
coated substrate.
BRIEF DESCRIPTION OF THE DRAWINGS
[1001] FIG. 1 is a graph showing the effect of comonomer on the
fastest crystallization half-times of modified PCT
copolyesters.
[1002] FIG. 2 is a graph showing the effect of comonomer on the
brittle-to-ductile transition temperature (T.sub.bd) in a notched
Izod test (ASTM D256, 1/8-in thick, 10-mil notch).
[1003] FIG. 3 is a graph showing the effect of
2,2,4,4-tetramethyl-1,3-cyclobutanediol composition on the glass
transition temperature (Tg) of the copolyester.
DETAILED DESCRIPTION OF THE INVENTION
[1004] The present invention may be understood more readily by
reference to the following detailed description of certain
embodiments of the invention and the working examples. In
accordance with the purpose(s) of this invention, certain
embodiments of the invention are described in the Summary of the
Invention and are further described herein below. Also, other
embodiments of the invention are described herein.
[1005] It is believed that medical devices comprising the
polyester(s) having the composition(s) described herein having the
compositions described above have a combination of two or more
physical properties such as high impact strength, moderate glass
transition temperatures, chemical resistance, hydrolytic stability,
toughness, low ductile-to-brittle transition temperatures, good
color and clarity, low densities, and long crystallization
half-times, good thermoformability, and good processability thereby
easily permitting them to be formed into articles. In some of the
embodiments of the invention, the polyesters have a unique
combination of the properties of good impact strength, heat
resistance, chemical resistance, density and/or the combination of
the properties of good impact strength, heat resistance, and
processability and/or the combination of two or more of the
described properties, that have never before been believed to be
present in a polyester.
[1006] The term "polyester", as used herein, is intended to include
"copolyesters" and is understood to mean a synthetic polymer
prepared by the reaction of one or more difunctional carboxylic
acids and/or multifunctional carboxylic acids with one or more
difunctional hydroxyl compounds and/or multifunctional hydroxyl
compounds. Typically the difunctional carboxylic acid can be a
dicarboxylic acid and the difunctional hydroxyl compound can be a
dihydric alcohol such as, for example, glycols and diols. The term
"glycol" as used in this application includes, but is not limited
to, diols, glycols, and/or multifunctional hydroxyl compounds.
Alternatively, the difunctional carboxylic acid may be a hydroxy
carboxylic acid such as, for example, p-hydroxybenzoic acid, and
the difunctional hydroxyl compound may be an aromatic nucleus
bearing 2 hydroxyl substituents such as, for example, hydroquinone.
The term "residue", as used herein, means any organic structure
incorporated into a polymer through a polycondensation and/or an
esterification reaction from the corresponding monomer. The term
"repeating unit", as used herein, means an organic structure having
a dicarboxylic acid residue and a diol residue bonded through a
carbonyloxy group. Thus, for example, the dicarboxylic acid
residues may be derived from a dicarboxylic acid monomer or its
associated acid halides, esters, salts, anhydrides, or mixtures
thereof. Furthermore, as used in this application, the term
"diacid" includes multifunctional acids such as branching agents.
As used herein, therefore, the term dicarboxylic acid is intended
to include dicarboxylic acids and any derivative of a dicarboxylic
acid, including its associated acid halides, esters, half-esters,
salts, half-salts, anhydrides, mixed anhydrides, or mixtures
thereof, useful in a reaction process with a diol to make
polyester. As used herein, the term "terephthalic acid" is intended
to include terephthalic acid itself and residues thereof as well as
any derivative of terephthalic acid, including its associated acid
halides, esters, half-esters, salts, half-salts, anhydrides, mixed
anhydrides, or mixtures thereof or residues thereof useful in a
reaction process with a diol to make polyester.
[1007] In one embodiment, terephthalic acid may be used as the
starting material. In another embodiment, dimethyl terephthalate
may be used as the starting material. In yet another embodiment,
mixtures of terephthalic acid and dimethyl terephthalate may be
used as the starting material and/or as an intermediate
material.
[1008] The polyesters useful in the medical devices of the present
invention typically can be prepared from dicarboxylic acids and
diols which react in substantially equal proportions and are
incorporated into the polyester polymer as their corresponding
residues. The polyesters useful in the medical devices of the
present invention, therefore, can contain substantially equal molar
proportions of acid residues (100 mole %) and diol (and/or
multifunctional hydroxyl compound) residues (100 mole %) such that
the total moles of repeating units is equal to 100 mole %. The mole
percentages provided in the present disclosure, therefore, may be
based on the total moles of acid residues, the total moles of diol
residues, or the total moles of repeating units. For example, a
polyester containing 30 mole % isophthalic acid, based on the total
acid residues, means the polyester contains 30 mole % isophthalic
acid residues out of a total of 100 mole % acid residues. Thus,
there are 30 moles of isophthalic acid residues among every 100
moles of acid residues. In another example, a polyester containing
25 mole % 2,2,4,4-tetramethyl-1,3-cyclobutanediol, based on the
total diol residues, means the polyester contains 25 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues out of a total of
100 mole % diol residues. Thus, there are 25 moles of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues among every 100
moles of diol residues.
[1009] In other aspects of the invention, the Tg of the polyesters
useful in the medical device(s) of the invention can be at least
one of the following ranges: 85 to 200.degree. C.; 85 to
190.degree. C.; 85 to 180.degree. C.; 85 to 170.degree. C.; 85 to
160.degree. C.; 85 to 155.degree. C.; 85 to 150.degree. C.; 85 to
145.degree. C.; 85 to 140.degree. C.; 85 to 138.degree. C.; 85 to
135.degree. C.; 85 to 130.degree. C.; 85 to 125.degree. C.; 85 to
120.degree. C.; 85 to 115.degree. C.; 85 to 110.degree. C.; 85 to
105.degree. C.; 85 to 100.degree. C.; 85 to 95.degree. C.; 85 to
90.degree. C.; 90 to 300.degree. C.; 90 to 190.degree. C.; 90 to
180.degree. C.; 90 to 170.degree. C.; 90 to 160.degree. C.; 90 to
155.degree. C.; 90 to 150.degree. C.; 90 to 145.degree. C.; 90 to
140.degree. C.; 90 to 138.degree. C.; 90 to 135.degree. C.; 90 to
130.degree. C.; 90 to 125.degree. C.; 90 to 120.degree. C.; 90 to
115.degree. C.; 90 to 110.degree. C.; 90 to 105.degree. C.; 90 to
100.degree. C.; 90 to 95.degree. C.; 95 to 200.degree. C.; 95 to
190.degree. C.; 95 to 180.degree. C.; 95 to 170.degree. C.; 95 to
160.degree. C.; 95 to 155.degree. C.; 95 to 150.degree. C.; 95 to
145.degree. C.; 95 to 140.degree. C.; 95 to 138.degree. C.; 95 to
135.degree. C.; 95 to 130.degree. C.; 95 to 125.degree. C.; 95 to
120.degree. C.; 95 to 115.degree. C.; 95 to 110.degree. C.; 95 to
105.degree. C.; 95 to 100.degree. C.; 100 to 300.degree. C.; 100 to
190.degree. C.; 100 to 180.degree. C.; 100 to 170.degree. C.; 100
to 160.degree. C.; 100 to 155.degree. C.; 100 to 150.degree. C.;
100 to 145.degree. C.; 100 to 140.degree. C.; 100 to 138.degree.
C.; 100 to 135.degree. C.; 100 to 130.degree. C.; 100 to
125.degree. C.; 100 to 120.degree. C.; 100 to 115.degree. C.; 100
to 110.degree. C.; 105 to 200.degree. C.; 105 to 190.degree. C.;
105 to 180.degree. C.; 105 to 170.degree. C.; 105 to 160.degree.
C.; 105 to 155.degree. C.; 105 to 150.degree. C.; 105 to
145.degree. C.; 105 to 140.degree. C.; 105 to 138.degree. C.; 105
to 135.degree. C.; 105 to 130.degree. C.; 105 to 125.degree. C.;
105 to 120.degree. C.; 105 to 115.degree. C.; 105 to 110.degree.
C.; 110 to 300.degree. C.; 110 to 190.degree. C.; 110 to
180.degree. C.; 110 to 170.degree. C.; 110 to 160.degree. C.; 110
to 155.degree. C.; 110 to 150.degree. C.; 110 to 145.degree. C.;
110 to 140.degree. C.; 110 to 138.degree. C.; 110 to 135.degree.
C.; 110 to 130.degree. C.; 110 to 125.degree. C.; 110 to
120.degree. C.; 110 to 115.degree. C.; 115 to 200.degree. C.; 115
to 190.degree. C.; 115 to 180.degree. C.; 115 to 170.degree. C.;
115 to 160.degree. C.; 115 to 155.degree. C.; 115 to 150.degree.
C.; 115 to 145.degree. C.; 115 to 140.degree. C.; 115 to
138.degree. C.; 115 to 135.degree. C.; 110 to 130.degree. C.; 115
to 125.degree. C.; 115 to 120.degree. C.; 120 to 300.degree. C.;
120 to 190.degree. C.; 120 to 180.degree. C.; 120 to 170.degree.
C.; 120 to 160.degree. C.; 120 to 155.degree. C.; 120 to
150.degree. C.; 120 to 145.degree. C.; 120 to 140.degree. C.; 120
to 138.degree. C.; 120 to 135.degree. C.; 120 to 130.degree. C.;
125 to 200.degree. C.; 125 to 190.degree. C.; 125 to 180.degree.
C.; 125 to 170.degree. C.; 125 to 160.degree. C.; 125 to
155.degree. C.; 125 to 150.degree. C.; 125 to 145.degree. C.; 125
to 140.degree. C.; 125 to 138.degree. C.; 125 to 135.degree. C.;
127 to 200.degree. C.; 127 to 190.degree. C.; 127 to 180.degree.
C.; 127 to 170.degree. C.; 127 to 160.degree. C.; 127 to
150.degree. C.; 127 to 145.degree. C.; 127 to 140.degree. C.; 127
to 138.degree. C.; 127 to 135.degree. C.; 130 to 300.degree. C.;
130 to 190.degree. C.; 130 to 180.degree. C.; 130 to 170.degree.
C.; 130 to 160.degree. C.; 130 to 155.degree. C.; 130 to
150.degree. C.; 130 to 145.degree. C.; 130 to 140.degree. C.; 130
to 138.degree. C.; 130 to 135.degree. C.; 135 to 200.degree. C.;
135 to 190.degree. C.; 135 to 180.degree. C.; 135 to 170.degree.
C.; 135 to 160.degree. C.; 135 to 155.degree. C.; 135 to
150.degree. C.; 135 to 145.degree. C.; 135 to 140.degree. C.; 140
to 300.degree. C.; 140 to 190.degree. C.; 140 to 180.degree. C.;
140 to 170.degree. C.; 140 to 160.degree. C.; 140 to 155.degree.
C.; 140 to 150.degree. C.; 140 to 145.degree. C.; 148 to
200.degree. C.; 148 to 190.degree. C.; 148 to 180.degree. C.; 148
to 170.degree. C.; 148 to 160.degree. C.; 148 to 155.degree. C.;
148 to 150.degree. C.; 150 to 300.degree. C.; 150 to 190.degree.
C.; 150 to 180.degree. C.; 150 to 170.degree. C.; 150 to 160; 155
to 190.degree. C.; 155 to 180.degree. C.; 155 to 170.degree. C.;
and 155 to 165.degree. C.
[1010] In other aspects of the invention, the glycol component for
the polyesters useful in the medical devices of the invention
include but are not limited to at least one of the following
combinations of ranges: 1 to 99 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 1 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 95 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 5 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 90 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 10 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 85 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 15 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 99 mole %
1,4-cyclohexanedimethanol, 1 to 75 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 70 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 65 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 60 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 40 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 55 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 50 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 50 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 45 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 55 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 40 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 60 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 35 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 65 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 30 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 70 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 25 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 75 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 20 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 80 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 15 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 85 to 99 mole %
1,4-cyclohexanedimethanol; 1 to 10 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 90 to 99 mole %
1,4-cyclohexanedimethanol; and 1 to 5 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 95 to 99 mole %
1,4-cyclohexanedimethanol.
[1011] In other aspects of the invention, the glycol component for
the polyesters useful in the medical devices of the invention
include but are not limited to at least one of the following
combinations of ranges: 5 to less than 50 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 50 to 95
mole % 1,4-cyclohexanedimethanol; 5 to 45 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 55 to 95 mole %
1,4-cyclohexanedimethanol; 5 to 40 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 60 to 95 mole %
1,4-cyclohexanedimethanol; 5 to 35 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 65 to 95 mole %
1,4-cyclohexanedimethanol; 5 to less than 35 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 65 to 95
mole % 1,4-cyclohexanedimethanol; 5 to 30 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 70 to 95 mole %
1,4-cyclohexanedimethanol; 5 to 25 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 75 to 95 mole %
1,4-cyclohexanedimethanol; 10 to less than 50 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 50 to 90
mole % 1,4-cyclohexanedimethanol; 10 to 45 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 55 to 90 mole %
1,4-cyclohexanedimethanol; 10 to 40 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 60 to 90 mole %
1,4-cyclohexanedimethanol; 10 to 35 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 65 to 90 mole % 1,4
-cyclohexanedimethanol; 10 to less than 35 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 65 up to
90 mole % 1,4-cyclohexanedimethanol; 10 to 30 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 70 to 90 mole %
1,4-cyclohexanedimethanol; 10 to 25 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 75 to 90
mole % 1,4-cyclohexanedimethanol; 15 to less than 50 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 50 up to
85 mole % 1,4-cyclohexanedimethanol; 15 to 45 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 55 to 85 mole %
1,4-cyclohexanedimethanol; 15 to 40 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 60 to 85 mole %
1,4-cyclohexanedimethanol; 15 to 35 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 65 to 85 mole %
1,4-cyclohexanedimethanol; 15 to 30 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 70 to 85 mole %
1,4-cyclohexanedimethanol; 15 to 25 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 75 to 85 mole %
1,4-cyclohexanedimethanol; and 17 to 23 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 77 to 83 mole %
1,4-cyclohexanedimethanol.
[1012] In other aspects of the invention, the glycol component for
the polyesters useful in the medical devices of the invention
include but are not limited to at least one of the following
combinations of ranges: 20 to 99 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 1 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 95 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 5 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 90 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 10 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 85 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 15 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 80 mole %
1,4-cyclohexanedimethanol, 20 to 75 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 70 mole % 2,2,4,4
-tetramethyl-1,3-cyclobutanediol and 30 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 65 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 60 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 40 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 55 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 50 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 50 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 45 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 55 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 40 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 60 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 35 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 65 to 80 mole %
1,4-cyclohexanedimethanol; 20 to 30 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 70 to 80 mole %
1,4-cyclohexanedimethanol; and 20 to 25 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 75 to 80 mole %
1,4-cyclohexanedimethanol.
[1013] In other aspects of the invention, the glycol component for
the polyesters useful in the medical devices of the invention
include but are not limited to at least one of the following
combinations of ranges: 25 to 99 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 1 to 75 mole %
1,4-cyclohexanedimethanol; 25 to 90 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 10 to 75 mole %
1,4-cyclohexanedimethanol; 25 to 85 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 15 to 75 mole %
1,4-cyclohexanedimethanol; 25 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 75 mole %
1,4-cyclohexanedimethanol, 25 to 75 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 75 mole %
1,4-cyclohexanedimethanol; 25 to 70 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 75 mole %
1,4-cyclohexanedimethanol; 25 to 65 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 75 mole %
1,4-cyclohexanedimethanol; 25 to 60 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 40 to 75 mole %
1,4-cyclohexanedimethanol; 25 to 55 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 75 mole %
1,4-cyclohexanedimethanol; 25 to 50 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 50 to 75 mole %
1,4-cyclohexanedimethanol; 25 to 45 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 55 to 75 mole %
1,4-cyclohexanedimethanol; 25 to 40 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 60 to 75 mole %
1,4-cyclohexanedimethanol; 25 to 35 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 65 to 75 mole %
1,4-cyclohexanedimethanol; 25 to 30 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 70 to 75 mole %
1,4-cyclohexanedimethanol; and 25 to 25 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 75 to 75 mole %
1,4-cyclohexanedimethanol.
[1014] In other aspects of the invention, the glycol component for
the polyesters useful in the medical devices of the invention
include but are not limited to at least one of the following
combinations of ranges: 35 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 65 mole %
1,4-cyclohexanedimethanol; 37 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 63 mole %
1,4-cyclohexanedimethanol; 40 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 60 mole %
1,4-cyclohexanedimethanol; 45 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 55 mole %
1,4-cyclohexanedimethanol; 50 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 50 mole %
1,4-cyclohexanedimethanol; greater than 50 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to less than 50 mole
% 1,4-cyclohexanedimethanol; 55 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 45 mole %
1,4-cyclohexanedimethanol; 60 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 40 mole %
1,4-cyclohexanedimethanol; 65 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 35 mole %
1,4-cyclohexanedimethanol; 70 to 80 mole % 2,2,4,4-tetramethyl-1,3
-cyclobutanediol and 20 to 30 mole % 1,4-cyclohexanedimethanol; 40
to 75 mole % 2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 60
mole % 1,4-cyclohexanedimethanol; 45 to 75 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 55 mole %
1,4-cyclohexanedimethanol; 50 to 75 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 50 mole %
1,4-cyclohexanedimethanol; 55 to 75 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 45 mole %
1,4-cyclohexanedimethanol; 60 to 75 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 40 mole %
1,4-cyclohexanedimethanol; 65 to 75 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 35 mole %
1,4-cyclohexanedimethanol; 40 to 70 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 60 mole %
1,4-cyclohexanedimethanol; 45 to 70 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 55 mole %
1,4-cyclohexanedimethanol; 50 to 70 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 50 mole %
1,4-cyclohexanedimethanol; greater than 50 to 99 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 1 to less than 55 mole
% 1,4-cyclohexanedimethanol; greater than 50 to 80 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to less than 50 mole
% 1,4-cyclohexanedimethanol; greater than 50 to 75 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to less than 50 mole
% 1,4-cyclohexanedimethanol; greater than 50 to 70 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to less than 50 mole
% 1,4-cyclohexanedimethanol; 55 to 70 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 45 mole %
1,4-cyclohexanedimethanol; 60 to 70 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 40 mole %
1,4-cyclohexanedimethanol; 40 to 65 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 60 mole %
1,4-cyclohexanedimethanol; 40 to 55 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 60 mole %
1,4-cyclohexanedimethanol; 40 to less than 45 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 55 to 60
mole % 1,4-cyclohexanedimethanol; 45 to 65 mole %
2,2,4,4-tetramethyl-1,3 -cyclobutanediol and 35 to 55 mole %
1,4-cyclohexanedimethanol; greater than 50 to 65 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to less than 50 mole
% 1,4-cyclohexanedimethanol; 50 to 65 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 50 mole %
1,4-cyclohexanedimethanol; 55 to 65 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 45 mole %
1,4-cyclohexanedimethanol; 40 to 60 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 40 to 60 mole %
1,4-cyclohexanedimethanol; 45 to 60 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 40 to 55 mole %
1,4-cyclohexanedimethanol; 45 to 55 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 55 mole %
1,4-cyclohexanedimethanol; greater than 45 to 55 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol; 45 to less than 55 mole %
1,4-cyclohexanedimethanol; and 46 to 55 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 54 mole %
1,4-cyclohexanedimethanol; and 46 to 65 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 54 mole %
1,4-cyclohexanedimethanol.
[1015] In addition to the diols set forth above, the polyesters
useful in the polyester compositions of the medical devices of the
invention may be made from 1,3-propanediol, 1,4-butanediol, or
mixtures thereof. It is contemplated that compositions of the
invention made from 1,3-propanediol, 1,4-butanediol, or mixtures
thereof can possess at least one of the Tg ranges described herein,
at least one of the inherent viscosity ranges described herein,
and/or at least one of the glycol or diacid ranges described
herein. In addition or in the alternative, the polyesters made from
1,3-propanediol or 1,4-butanediol or mixtures thereof may also be
made from 1,4-cyclohexanedimethanol in at least one of the
following amounts: from 0.1 to 99 mole %; from 0.1 to 80 mole %;
from 0.1 to 70 mole %; from 0.1 to 60 mole %; from 0.1 to 50 mole
%; from 0.1 to 40 mole %; from 0.1 to 35 mole %; from 0.1 to 30
mole %; from 0.1 to 25 mole %; from 0.1 to 20 mole %; from 0.1 to
15 mole %; from 0.1 to 10 mole %; from 0.1 to 5 mole %; from 1 to
99 mole %; from 1 to 80 mole %; from 1 to 70 mole %; from 1 to 60
mole %; from 1 to 50 mole %; from 1 to 40 mole %; from 1 to 35 mole
%; from 1 to 30 mole %; from 1 to 25 mole %; from 1 to 20 mole %;
from 1 to 15 mole %; from 1 to 10 mole %; from 1 to 5 mole %; from
5 to 80 mole %; 5 to 70 mole %; from 5 to 60 mole %; from 5 to 50
mole %; from 5 to 40 mole %; from 5 to 35 mole %; from 5 to 30 mole
%; from 5 to 25 mole %; from 5 to 20 mole %; and from 5 to 15 mole
%; from 5 to 10 mole %; from 10 to 99 mole %; from 10 to 80 mole %;
from 10 to 70 mole %; from 10 to 60 mole %; from 10 to 50 mole %;
from 10 to 40 mole %; from 10 to 35 mole %; from 10 to 30 mole %;
from 10 to 25 mole %; from 10 to 20 mole %; from 10 to 15 mole %;
from 20 to 99 mole %; from 20 to 80 mole %; from 20 to 70 mole %;
from 20 to 60 mole %; from 20 to 50 mole %; from 20 to 40 mole %;
from 20 to 35 mole %; from 20 to 30 mole %; and from 20 to 25 mole
%.
[1016] For embodiments of the invention, the polyesters useful in
the invention may exhibit at least one of the following inherent
viscosities as determined in 60/40 (wt/wt) phenol/tetrachloroethane
at a concentration of 0.5 g/100 ml at 25.degree. C.: 0.10 to 1.2
dL/g; 0.10 to 1.1 dL/g; 0.10 to 1 dL/g; 0.10 to less than 1 dL/g;
0.10 to 0.98 dL/g; 0.10 to 0.95 dL/g; 0.10 to 0.90 dL/g; 0.10 to
0.85 dL/g; 0.10 to 0.80 dL/g; 0.10 to 0.75 dL/g; 0.10 to less than
0.75 dL/g; 0.10 to 0.72 dL/g; 0.10 to 0.70 dL/g; 0.10 to less than
0.70 dL/g; 0.10 to 0.68 dL/g; 0.10 to less than 0.68 dL/g; 0.10 to
0.65 dL/g; 0.20 to 1.2 dL/g; 0.20 to 1.1 dL/g; 0.20 to 1 dL/g; 0.20
to less than 1 dL/g; 0.20 to 0.98 dL/g; 0.20 to 0.95 dL/g; 0.20 to
0.90 dL/g; 0.20 to 0.85 dL/g; 0.20 to 0.80 dL/g; 0.20 to 0.75 dL/g;
0.20 to less than 0.75 dL/g; 0.20 to 0.72 dL/g; 0.20 to 0.70 dL/g;
0.20 to less than 0.70 dL/g; 0.20 to 0.68 dL/g; 0.20 to less than
0.68 dL/g; 0.20 to 0.65 dL/g; 0.35 to 1.2 dL/g; 0.35 to 1.1 dL/g;
0.35 to 1 dL/g; 0.35 to less than 1 dL/g; 0.35 to 0.98 dL/g; 0.35
to 0.95 dL/g; 0.35 to 0.90 dL/g; 0.35 to 0.85 dL/g; 0.35 to 0.80
dL/g; 0.35 to 0.75 dL/g; 0.35 to less than 0.75 dL/g; 0.35 to 0.72
dL/g; 0.35 to 0.70 dL/g; 0.35 to less than 0.70 dL/g; 0.35 to 0.68
dL/g; 0.35 to less than 0.68 dL/g; 0.35 to 0.65 dL/g; 0.40 to 1.2
dL/g; 0.40 to 1.1 dL/g; 0.40 to 1 dL/g; 0.40 to less than 1 dL/g;
0.40 to 0.98 dL/g; 0.40 to 0.95 dL/g; 0.40 to 0.90 dL/g; 0.40 to
0.85 dL/g; 0.40 to 0.80 dL/g; 0.40 to 0.75 dL/g; 0.40 to less than
0.75 dL/g; 0.40 to 0.72 dL/g; 0.40 to 0.70 dL/g; 0.40 to less than
0.70 dL/g; 0.40 to 0.68 dL/g; 0.40 to less than 0.68 dL/g; 0.40 to
0.65 dL/g; greater than 0.42 to 1.2 dL/g; greater than 0.42 to 1.1
dL/g; greater than 0.42 to 1 dL/g; greater than 0.42 to less than 1
dL/g; greater than 0.42 to 0.98 dL/g; greater than 0.42 to 0.95
dL/g; greater than 0.42 to 0.90 dL/g; greater than 0.42 to 0.85
dL/g; greater than 0.42 to 0.80 dL/g; greater than 0.42 to 0.75
dL/g; greater than 0.42 to less than 0.75 dL/g; greater than 0.42
to 0.72 dL/g; greater than 0.42 to less than 0.70 dL/g; greater
than 0.42 to 0.68 dL/g; greater than 0.42 to less than 0.68 dL/g;
and greater than 0.42 to 0.65 dL/g.
[1017] For embodiments of the invention, the polyesters useful in
the invention may exhibit at least one of the following inherent
viscosities as determined in 60/40 (wt/wt) phenol/tetrachloroethane
at a concentration of 0.5 g/100 ml at 25.degree. C.: 0.45 to 1.2
dL/g; 0.45 to 1.1 dL/g; 0.45 to 1 dL/g; 0.45 to 0.98 dL/g; 0.45 to
0.95 dL/g; 0.45 to 0.90 dL/g; 0.45 to 0.85 dL/g; 0.45 to 0.80 dL/g;
0.45 to 0.75 dL/g; 0.45 to less than 0.75 dL/g; 0.45 to 0.72 dL/g;
0.45 to 0.70 dL/g; 0.45 to less than 0.70 dL/g; 0.45 to 0.68 dL/g;
0.45 to less than 0.68 dL/g; 0.45 to 0.65 dL/g; 0.50 to 1.2 dL/g;
0.50 to 1.1 dL/g; 0.50 to 1 dL/g; 0.50 to less than 1 dL/g; 0.50 to
0.98 dL/g; 0.50 to 0.95 dL/g; 0.50 to 0.90 dL/g; 0.50 to 0.85 dL/g;
0.50 to 0.80 dL/g; 0.50 to 0.75 dL/g; 0.50 to less than 0.75 dL/g;
0.50 to 0.72 dL/g; 0.50 to 0.70 dL/g; 0.50 to less than 0.70 dL/g;
0.50 to 0.68 dL/g; 0.50 to less than 0.68 dL/g; 0.50 to 0.65 dL/g;
0.55 to 1.2 dL/g; 0.55 to 1.1 dL/g; 0.55 to 1 dL/g; 0.55 to less
than 1 dL/g; 0.55 to 0.98 dL/g; 0.55 to 0.95 dL/g; 0.55 to 0.90
dL/g; 0.55 to 0.85 dL/g; 0.55 to 0.80 dL/g; 0.55 to 0.75 dL/g; 0.55
to less than 0.75 dL/g; 0.55 to 0.72 dL/g; 0.55 to 0.70 dL/g; 0.55
to less than 0.70 dL/g; 0.55 to 0.68 dL/g; 0.55 to less than 0.68
dL/g; 0.55 to 0.65 dL/g; 0.58 to 1.2 dL/g; 0.58 to 1.1 dL/g; 0.58
to 1 dL/g; 0.58 to less than 1 dL/g; 0.58 to 0.98 dL/g; 0.58 to
0.95 dL/g; 0.58 to 0.90 dL/g; 0.58 to 0.85 dL/g; 0.58 to 0.80 dL/g;
0.58 to 0.75 dL/g; 0.58 to less than 0.75 dL/g; 0.58 to 0.72 dL/g;
0.58 to 0.70 dL/g; 0.58 to less than 0.70 dL/g; 0.58 to 0.68 dL/g;
0.58 to less than 0.68 dL/g; 0.58 to 0.65 dL/g; 0.60 to 1.2 dL/g;
0.60 to 1.1 dL/g; 0.60 to 1 dL/g; 0.60 to less than 1 dL/g; 0.60 to
0.98 dL/g; 0.60 to 0.95 dL/g; 0.60 to 0.90 dL/g; 0.60 to 0.85 dL/g;
0.60 to 0.80 dL/g; 0.60 to 0.75 dL/g; 0.60 to less than 0.75 dL/g;
0.60 to 0.72 dL/g; 0.60 to 0.70 dL/g; 0.60 to less than 0.70 dL/g;
0.60 to 0.68 dL/g; 0.60 to less than 0.68 dL/g; 0.60 to 0.65 dL/g;
0.65 to 1.2 dL/g; 0.65 to 1.1 dL/g; 0.65 to 1 dL/g; 0.65 to less
than 1 dL/g; 0.65 to 0.98 dL/g; 0.65 to 0.95 dL/g; 0.65 to 0.90
dL/g; 0.65 to 0.85 dL/g; 0.65 to 0.80 dL/g; 0.65 to 0.75 dL/g; 0.65
to less than 0.75 dL/g; 0.65 to 0.72 dL/g; 0.65 to 0.70 dL/g; 0.65
to less than 0.70 dL/g; 0.68 to 1.2 dL/g; 0.68 to 1.1 dL/g; 0.68 to
1 dL/g; 0.68 to less than 1 dL/g; 0.68 to 0.98 dL/g; 0.68 to 0.95
dL/g; 0.68 to 0.90 dL/g; 0.68 to 0.85 dL/g; 0.68 to 0.80 dL/g; 0.68
to 0.75 dL/g; 0.68 to less than 0.75 dL/g; 0.68 to 0.72 dL/g;
greater than 0.76 dL/g to 1.2 dL/g; greater than 0.76 dL/g to 1.1
dL/g; greater than 0.76 dL/g to 1 dL/g; greater than 0.76 dL/g to
less than 1 dL/g; greater than 0.76 dL/g to 0.98 dL/g; greater than
0.76 dL/g to 0.95 dL/g; greater than 0.76 dL/g to 0.90 dL/g;
greater than 0.80 dL/g to 1.2 dL/g; greater than 0.80 dL/g to 1.1
dL/g; greater than 0.80 dL/g to 1 dL/g; greater than 0.80 dL/g to
less than 1 dL/g; greater than 0.80 dL/g to 1.2 dL/g; greater than
0.80 dL/g to 0.98 dL/g; greater than 0.80 dL/g to 0.95 dL/g;
greater than 0.80 dL/g to 0.90 dL/g.
[1018] It is contemplated that compositions useful in the medical
device(s) of the invention can possess at least one of the inherent
viscosity ranges described herein and at least one of the monomer
ranges for the compositions described herein unless otherwise
stated. It is also contemplated that compositions useful in the
medical device(s) of the invention can possess at least one of the
Tg ranges described herein and at least one of the monomer ranges
for the compositions described herein unless otherwise stated. It
is also contemplated that compositions useful in the medical
device(s) of the invention can posses at least one of the inherent
viscosity ranges described herein, at least one of the Tg ranges
described herein, and at least one of the monomer ranges for the
compositions described herein unless otherwise stated.
[1019] For the desired polyester, the molar ratio of cis/trans
2,2,4,4-tetramethyl-1,3-cyclobutanediol can vary from the pure form
of each or mixtures thereof. In certain embodiments, the molar
percentages for cis and/or trans
2,2,4,4-tetramethyl-1,3-cyclobutanediol are greater than 50 mole %
cis and less than 50 mole % trans; or greater than 55 mole % cis
and less than 45 mole % trans; or 30 to 70 mole % cis and 70 to 30%
trans; or 40 to 60 mole % cis and 60 to 40 mole % trans; or 50 to
70 mole % trans and 50 to 30% cis or 50 to 70 mole % cis and 50 to
30% trans; or 60 to 70 mole % cis and 30 to 40 mole % trans; or
greater than 70 mole % cis and less than 30 mole % trans; wherein
the total sum of the mole percentages for cis- and
trans-2,2,4,4-tetramethyl-1,3-cyclobutanediol is equal to 100 mole
%. The molar ratio of cis/trans 1,4-cyclohexanedimethanol can vary
within the range of 50/50 to 0/100, for example, between 40/60 to
20/80.
[1020] In certain embodiments, terephthalic acid, an ester thereof,
such as, for example, dimethyl terephthalate, or a mixture of
terephthalic acid and an ester thereof, makes up most or all of the
dicarboxylic acid component used to form the polyesters useful in
the invention. In certain embodiments, terephthalic acid residues
can make up a portion or all of the dicarboxylic acid component
used to form the present polyester at a concentration of at least
70 mole %, such as at least 80 mole %, at least 90 mole %, at least
95 mole %, at least 99 mole %, or a mole % of 100. In certain
embodiments, higher amounts of terephthalic acid can be used in
order to produce a higher impact strength polyester. For the
purposes of this disclosure, the terms "terephthalic acid" and
"dimethyl terephthalate" are used interchangeably herein. In one
embodiment, dimethyl terephthalate is part or all of the
dicarboxylic acid component used to make the polyesters useful in
the present invention. In all embodiments, ranges of from 70 to 100
mole %; or 80 to 100 mole %; or 90 to 100 mole %; or 99 to 100 mole
%; or 100 mole % terephthalic acid and/or dimethyl terephthalate
and/or mixtures thereof may be used.
[1021] In addition to terephthalic acid residues, the dicarboxylic
acid component of the polyesters useful in the medical devices and
methods of the present invention can comprise up to 30 mole %, up
to 20 mole %, up to 10 mole %, up to 5 mole %, or up to 1 mole %
modifying aromatic dicarboxylic acids. Yet another embodiment
contains 0 mole % modifying aromatic dicarboxylic acids. Thus, if
present, it is contemplated that the amount of one or more
modifying aromatic dicarboxylic acids can range from any of these
preceding endpoint values including, for example, from 0.01 to 30
mole %, 0.01 to 20 mole %, from 0.01 to 10 mole %, from 0.01 to 5
mole % and from 0.01 to 1 mole. In one embodiment, modifying
aromatic dicarboxylic acids that may be used in the present
invention include but are not limited to those having up to 20
carbon atoms, and which can be linear, para-oriented, or
symmetrical. Examples of modifying aromatic dicarboxylic acids
which may be used in this invention include, but are not limited
to, isophthalic acid, 4,4'-biphenyldicarboxylic acid, 1,4-, 1,5-,
2,6-, 2,7-naphthalenedicarboxylic acid, and
trans-4,4'-stilbenedicarboxylic acid, and esters thereof. In one
embodiment, the modifying aromatic dicarboxylic acid is isophthalic
acid.
[1022] In addition to terephthalic acid residues, the dicarboxylic
acid component of the polyesters useful in the invention can
comprise up to 30 mole %, up to 20 mole %, up to 10 mole %, up to 5
mole %, or up to 1 mole % modifying aromatic dicarboxylic acids.
Yet another embodiment contains 0 mole % modifying aromatic
dicarboxylic acids. Thus, if present, it is contemplated that the
amount of one or more modifying aromatic dicarboxylic acids can
range from any of these preceding endpoint values including, for
example, from 0.01 to 30 mole %, 0.01 to 20 mole %, from 0.01 to 10
mole %, from 0.01 to 5 mole % and from 0.01 to 1 mole. In one
embodiment, modifying aromatic dicarboxylic acids that may be used
in the present invention include but are not limited to those
having up to 20 carbon atoms, and which can be linear,
para-oriented, or symmetrical. Examples of modifying aromatic
dicarboxylic acids which may be used in this invention include, but
are not limited to, isophthalic acid, 4,4'-biphenyldicarboxylic
acid, 1,4-, 1,5-, 2,6-, 2,7-naphthalenedicarboxylic acid, and
trans-4,4'-stilbenedicarboxylic acid, and esters thereof. In one
embodiment, the modifying aromatic dicarboxylic acid is isophthalic
acid.
[1023] The carboxylic acid component of the polyesters useful in
the medical devices of the invention can be further modified with
up to 10 mole %, up to 5 mole % or up to 1 mole % of one or more
aliphatic dicarboxylic acids containing 2-16 carbon atoms, such as,
for example, malonic, succinic, glutaric, adipic, pimelic, suberic,
azelaic and dodecanedioic dicarboxylic acids. Certain embodiments
can also comprise 0.01 or more mole %, 0.1 or more mole %, 1 or
more mole %, 5 or more mole %, or 10 or more mole % of one or more
modifying aliphatic dicarboxylic acids. Yet another embodiment
contains 0 mole % modifying aliphatic dicarboxylic acids. Thus, if
present, it is contemplated that the amount of one or more
modifying aliphatic dicarboxylic acids can range from any of these
preceding endpoint values including, for example, from 0.01 to 10
mole % and from 0.1 to 10 mole %. The total mole % of the
dicarboxylic acid component is 100 mole %.
[1024] Esters of terephthalic acid and the other modifying
dicarboxylic acids or their corresponding esters and/or salts may
be used instead of the dicarboxylic acids. Suitable examples of
dicarboxylic acid esters include, but are not limited to, the
dimethyl, diethyl, dipropyl, diisopropyl, dibutyl, and diphenyl
esters. In one embodiment, the esters are chosen from at least one
of the following: methyl, ethyl, propyl, isopropyl, and phenyl
esters.
[1025] The 1,4-cyclohexanedimethanol may be cis, trans, or a
mixture thereof, such as a cis/trans ratio of 60:40 to 40:60. In
another embodiment, the trans-1,4-cyclohexanedimethanol can be
present in an amount of 60 to 80 mole %.
[1026] The glycol component of the polyester portion of the
polyester composition useful in the invention can contain 25 mole %
or less of one or more modifying glycols which are not
2,2,4,4-tetramethyl-1,3-cyclobutanediol or
1,4-cyclohexanedimethanol; in one embodiment, the polyester useful
in the invention may contain less than 15 mole % of one or more
modifying glycols. In another embodiment, the polyesters useful in
the invention can contain 10 mole % or less of one or more
modifying glycols. In another embodiment, the polyesters useful in
the invention can contain 5 mole % or less of one or more modifying
glycols. In another embodiment, the polyesters useful in the
invention can contain 3 mole % or less of one or more modifying
glycols. In another embodiment, the polyesters useful in the
invention can contain 0 mole % of one or more modifying glycols.
Certain embodiments can also contain 0.01 or more mole %, such as
0.1 or more mole %, 1 or more mole %, 5 or more mole %, or 10 or
more mole % of one or more modifying glycols. Thus, if present, it
is contemplated that the amount of one or more modifying glycols
can range from any of these preceding endpoint values including,
for example, from 0.01 to 15 mole % and from 0.1 to 10 mole %.
[1027] Modifying glycols useful in the polyester useful in the
invention refer to diols other than
2,2,4,4-tetramethyl-1,3-cyclobutanediol and
1,4-cyclohexanedimethanol and may contain 2 to 16 carbon atoms.
Examples of suitable modifying glycols include, but are not limited
to, ethylene glycol residues, 1,2-propanediol, 1,3-propanediol,
neopentyl glycol, 1,4-butanediol, 1,5-pentanediol, 1,6-hexanediol,
p-xylene glycol or mixtures thereof. In one embodiment, the
modifying glycol is ethylene glycol residues. In another
embodiment, the modifying glycols are 1,3-propanediol and/or
1,4-butanediol. In another embodiment, ethylene glycol residues are
excluded as a modifying diol. In another embodiment,
1,3-propanediol and 1,4-butanediol are excluded as modifying diols.
In another embodiment, 2,2-dimethyl-1,3-propanediol is excluded as
a modifying diol.
[1028] The polyesters and/or the polycarbonates useful in the
invention can comprise from 0 to 10 weight percent (wt %), for
example, from 0.01 to 5 weight percent, from 0.01 to 1 weight
percent, from 0.05 to 5 weight percent, from 0.05 to 1 weight
percent, or from 0.1 to 0.7 weight percent, based on the total
weight of the polyester and/or polycarbonate, respectively, of one
or more residues of a branching monomer, also referred to herein as
a branching agent, having 3 or more carboxyl substituents, hydroxyl
substituents, or a combination thereof. In certain embodiments, the
branching monomer or agent may be added prior to and/or during
and/or after the polymerization of the polyester. The polyester(s)
useful in the invention can thus be linear or branched. The
polycarbonate can also be linear or branched. In certain
embodiments, the branching monomer or agent may be added prior to
and/or during and/or after the polymerization of the
polycarbonate.
[1029] Examples of branching monomers include, but are not limited
to, multifunctional acids or multifunctional alcohols such as
trimellitic acid, trimellitic anhydride, pyromellitic dianhydride,
trimethylolpropane, glycerol, pentaerythritol, citric acid,
tartaric acid, 3-hydroxyglutaric acid and the like. In one
embodiment, the branching monomer residues comprise 0.1 to 0.7 mole
percent of one or more residues of: trimellitic anhydride,
pyromellitic dianhydride, glycerol, sorbitol, 1,2,6-hexanetriol,
pentaerythritol, trimethylolethane, or trimesic acid. The branching
monomer may be added to the polyester reaction mixture or blended
with the polyester in the form of a concentrate as described, for
example, in U.S. Pat. Nos. 5,654,347 and 5,696,176, the disclosure
regarding branching monomers which is incorporated herein by
reference.
[1030] The carboxylic acid component of the polyesters useful in
the medical devices and methods of the present invention can be
further modified with up to 10 mole %, up to 5 mole % or up to 1
mole % of one or more aliphatic dicarboxylic acids containing 2-16
carbon atoms, such as, for example, malonic, succinic, glutaric,
adipic, pimelic, suberic, azelaic and dodecanedioic dicarboxylic
acids. Certain embodiments can also comprise 0.01 or more mole %,
0.1 or more mole %, 1 or more mole %, 5 or more mole %, or 10 or
more mole % of one or more modifying aliphatic dicarboxylic acids.
Yet another embodiment contains 0 mole % modifying aliphatic
dicarboxylic acids. Thus, if present, it is contemplated that the
amount of one or more modifying aliphatic dicarboxylic acids can
range from any of these preceding endpoint values including, for
example, from 0.01 to 10 mole % and from 0.1 to 10 mole %. The
total mole % of the dicarboxylic acid component is 100 mole %.
[1031] Esters of terephthalic acid and the other modifying
dicarboxylic acids or their corresponding esters and/or salts may
be used instead of the dicarboxylic acids. Suitable examples of
dicarboxylic acid esters include, but are not limited to, the
dimethyl, diethyl, dipropyl, diisopropyl, dibutyl, and diphenyl
esters. In one embodiment, the esters are chosen from at least one
of the following: methyl, ethyl, propyl, isopropyl, and phenyl
esters.
[1032] The 1,4-cyclohexanedimethanol may be cis, trans, or a
mixture thereof, such as a cis/trans ratio of 60:40 to 40:60. In
another embodiment, the trans-1,4-cyclohexanedimethanol can be
present in an amount of 60 to 80 mole %.
[1033] The glycol component of the polyester portion of the
polyester composition useful in the invention can contain 25 mole %
or less of one or more modifying glycols which are not
2,2,4,4-tetramethyl-1,3-cyclobutanediol or
1,4-cyclohexanedimethanol; in one embodiment, the polyester useful
in the invention may contain less than 15 mole % or of one or more
modifying glycols. In another embodiment, the polyesters useful in
the invention can contain 10 mole % or less of one or more
modifying glycols. In another embodiment, the polyesters useful in
the invention can contain 5 mole % or less of one or more modifying
glycols. In another embodiment, the polyesters useful in the
invention can contain 3 mole % or less of one or more modifying
glycols. In another embodiment, the polyesters useful in the
invention can contain 0 mole % modifying glycols. Thus, if present,
it is contemplated that the amount of one or more modifying glycols
can range from any of these preceding endpoint values including,
for example, from 0.01 to 15 mole % and from 0.1 to 10 mole %.
[1034] Modifying glycols useful in polyesters useful in the
invention refer to diols other than
2,2,4,4-tetramethyl-1,3-cyclobutanediol and
1,4-cyclohexanedimethanol and can contain 2 to 16 carbon atoms.
Examples of suitable modifying glycols include, but are not limited
to, ethylene glycol, diethylene glycol, 1,2-propanediol,
1,3-propanediol, neopentyl glycol, 1,4-butanediol, 1,5-pentanediol,
1,6-hexanediol, p-xylene glycol, or mixtures thereof. One
embodiment for the modifying glycol is ethylene glycol. Other
modifying glycols include, but are not limited to, 1,3-propanediol
and 1,4-butanediol. In another embodiment, ethylene glycol is
excluded as a modifying diol. In another embodiment,
1,3-propanediol and 1,4-butanediol are excluded as modifying diols.
In another embodiment, 2,2-dimethyl-1,3-propanediol is excluded as
a modifying diol.
[1035] The polyesters and/or the polycarbonates useful in the
polyesters compositions of the invention can comprise from 0 to 10
mole percent, for example, from 0.01 to 5 mole percent, from 0.01
to 1 mole percent, from 0.05 to 5 mole percent, from 0.05 to 1 mole
percent, or from 0.1 to 0.7 mole percent, or 0.1 to 0.5 mole
percent, based the total mole percentages of either the diol or
diacid residues; respectively, of one or more residues of a
branching monomer, also referred to herein as a branching agent,
having 3 or more carboxyl substituents, hydroxyl substituents, or a
combination thereof. In certain embodiments, the branching monomer
or agent may be added prior to and/or during and/or after the
polymerization of the polyester. The polyester(s) useful in the
invention can thus be linear or branched. The polycarbonate can
also be linear or branched. In certain embodiments, the branching
monomer or agent may be added prior to and/or during and/or after
the polymerization of the polycarbonate.
[1036] Examples of branching monomers include, but are not limited
to, multifunctional acids or multifunctional alcohols such as
trimellitic acid, trimellitic anhydride, pyromellitic dianhydride,
trimethylolpropane, glycerol, pentaerythritol, citric acid,
tartaric acid, 3-hydroxyglutaric acid and the like. In one
embodiment, the branching monomer residues can comprise 0.1 to 0.7
mole percent of one or more residues chosen from at least one of
the following: trimellitic anhydride, pyromellitic dianhydride,
glycerol, sorbitol, 1,2,6-hexanetriol, pentaerythritol,
trimethylolethane, and/or trimesic acid. The branching monomer may
be added to the polyester reaction mixture or blended with the
polyester in the form of a concentrate as described, for example,
in U.S. Pat. Nos. 5,654,347 and 5,696,176, whose disclosure
regarding branching monomers is incorporated herein by
reference.
[1037] The glass transition temperature (Tg) of the polyesters
useful in the medical devices and methods of the present invention
was determined using a TA DSC 2920 from Thermal Analyst Instrument
at a scan rate of 20.degree. C./min.
[1038] Because of the long crystallization half-times (e.g.,
greater than 5 minutes) at 170.degree. C. exhibited by certain
polyesters useful in the present invention, it can be possible to
produce articles, such as medical devices, including, but not
limited to, injection molded parts, injection blow molded articles,
injection stretch blow molded articles, extruded film, extruded
sheet, extrusion blow molded articles, extrusion stretch blow
molded articles, and fibers. A thermoformable sheet is an example
of an article of manufacture provided by this invention. The
polyesters of the invention can be amorphous or semicrystalline. In
one aspect, certain polyesters useful in the invention can have a
relatively low crystallinity. Certain polyesters useful in the
invention can thus have a substantially amorphous morphology,
meaning that the polyesters comprise substantially unordered
regions of polymer.
[1039] In one embodiment, an "amorphous" polyester can have a
crystallization half-time of greater than 5 minutes at 170.degree.
C.; or greater than 10 minutes at 170.degree. C.; or greater than
50 minutes at 170.degree. C.; or greater than 100 minutes at
170.degree. C. or greater than 100 minutes at 170.degree. C. In one
embodiment, of the invention, the crystallization half-times can be
greater than 1,000 minutes at 170.degree. C. In another embodiment
of the invention, the crystallization half-times of the polyesters
useful in the invention can be greater than 10,000 minutes at
170.degree. C. The crystallization half time of the polyester, as
used herein, may be measured using methods well-known to persons of
skill in the art. For example, the crystallization half time of the
polyester, t.sub.1/2, can be determined by measuring the light
transmission of a sample via a laser and photo detector as a
function of time on a temperature controlled hot stage. This
measurement can be done by exposing the polymers to a temperature,
T.sub.max, and then cooling it to the desired temperature. The
sample can then be held at the desired temperature by a hot stage
while transmission measurements are made as a function of time.
Initially, the sample can be visually clear with high light
transmission, and becomes opaque as the sample crystallizes. The
crystallization half-time is the time at which the light
transmission is halfway between the initial transmission and the
final transmission. T.sub.max is defined as the temperature
required to melt the crystalline domains of the sample (if
crystalline domains are present). The sample can be heated to Tmax
to condition the sample prior to crystallization half time
measurement. The absolute Tmax temperature is different for each
composition. For example PCT can be heated to some temperature
greater than 290.degree. C. to melt the crystalline domains.
[1040] As shown in Table 1 and FIG. 1 of the Examples,
2,2,4,4-tetramethyl-1,3-cyclobutanediol is more effective than
other comonomers such ethylene glycol and isophthalic acid at
increasing the crystallization half-time, i.e., the time required
for a polymer to reach half of its maximum crystallinity. By
decreasing the crystallization rate of PCT, i.e. increasing the
crystallization half-time, amorphous articles based on modified,
PCT may be fabricated by methods known in the art such as
extrusion, injection molding, and the like. As shown in Table 1,
these materials can exhibit higher glass transition temperatures
and lower densities than other modified PCT copolyesters.
[1041] The polyesters can exhibit an improvement in toughness
combined with processability for some of the embodiments of the
invention. For example, lowering the inherent viscosity slightly of
the polyesters useful in the invention results in a more
processable melt viscosity while retaining good physical properties
of the polyesters such as toughness and heat resistance.
[1042] Increasing the content of 1,4-cyclohexanedimethanol in a
copolyester based on terephthalic acid, ethylene glycol, and
1,4-cyclohexanedimethanol can improve toughness, which can be
determined by the brittle-to-ductile transition temperature in a
notched Izod impact strength test as measured by ASTM D256. This
toughness improvement, by lowering of the brittle-to-ductile
transition temperature with 1,4-cyclohexanedimethanol, is believed
to occur due to the flexibility and conformational behavior of
1,4-cyclohexanedimethanol in the copolyester. Incorporating
2,2,4,4-tetramethyl-1,3-cyclobutanediol into PCT is believed to
improve toughness, by lowering the brittle-to-ductile transition
temperature, as shown in Table 2 and FIG. 2 of the Examples.
[1043] In one embodiment, the melt viscosity of the polyester(s)
useful in the invention is less than 30,000 poise as measured a 1
radian/second on a rotary melt rheometer at 290.degree. C. In
another embodiment, the melt viscosity of the polyester(s) useful
in the invention is less than 20,000 poise as measured a 1
radian/second on a rotary melt rheometer at 290.degree. C.
[1044] In one embodiment, the melt viscosity of the polyester(s)
useful in the invention is less than 15,000 poise as measured at 1
radian/second (rad/sec) on a rotary melt rheometer at 290.degree.
C. In one embodiment, the melt viscosity of the polyester(s) useful
in the invention is less than 10,000 poise as measured at 1
radian/second (rad/sec) on a rotary melt rheometer at 290.degree.
C. In another embodiment, the melt viscosity of the polyester(s)
useful in the invention is less than 6,000 poise as measured at 1
radian/second on a rotary melt rheometer at 290.degree. C.
Viscosity at rad/sec is related to processability. Typical polymers
have viscosities of less than 10,000 poise as measured at 1
radian/second when measured at their processing temperature.
Polyesters are typically not processed above 290.degree. C.
Polycarbonate is typically processed at 290.degree. C. The
viscosity at 1 rad/sec of a typical 12 melt flow rate polycarbonate
is 7000 poise at 290.degree. C.
[1045] In one embodiment of the invention, the polyesters useful in
the invention exhibit superior notched Izod impact strength in
thick sections. Notched Izod impact strength, as described in ASTM
D256, is a common method of measuring toughness. When tested by the
Izod method, polymers can exhibit either a complete break failure
mode, where the test specimen breaks into two distinct parts, or a
partial or no break failure mode, where the test specimen remains
as one part. The complete break failure mode is associated with low
energy failure. The partial and no break failure modes are
associated with high energy failure. A typical thickness used to
measure Izod toughness is 1/8''. At this thickness, very few
polymers are believed to exhibit a partial or no break failure
mode, polycarbonate being one notable example. When the thickness
of the test specimen is increased to 1/4'', however, no commercial
amorphous materials exhibit a partial or no break failure mode. In
one embodiment, compositions of the present example exhibit a no
break failure mode when tested in Izod using a 1/4'' thick
specimen.
[1046] The present polyesters useful in this invention can possess
one or more of the following properties: In one embodiment, the
polyesters useful in the invention exhibit a notched Izod impact
strength of at least 150 J/m (3 ft-lb/in) at 23.degree. C. with a
10-mil notch in a 3.2 mm (1/8-inch) thick bar determined according
to ASTM D256; in one embodiment, the polyesters useful in the
invention exhibit a notched Izod impact strength of at least (400
J/m) 7.5 ft-lb/in at 23.degree. C. with a 10-mil notch in a 3.2 mm
(1/8-inch) thick bar determined according to ASTM D256; in one
embodiment, the polyesters useful in the invention exhibit a
notched Izod impact strength of at least 1000 J/m (18 ft-lb/in) at
23.degree. C. with a 10-mil notch in a 3.2 mm (1/8-inch) thick bar
determined according to ASTM D256. In one embodiment, the
polyesters useful in the invention exhibit a notched Izod impact
strength of at least 150 J/m (3 ft-lb/in) at 23.degree. C. with a
10-mil notch in a 6.4 mm (1/4-inch) thick bar determined according
to ASTM D256; in one embodiment, the polyesters useful in the
invention exhibit a notched Izod impact strength of at least (400
J/m) 7.5 ft-lb/in at 23.degree. C. with a 10-mil notch in a 6.4 mm
(1/4-inch) thick bar determined according to ASTM D256; in one
embodiment, the polyesters useful in the invention exhibit a
notched Izod impact strength of at least 1000 J/m (18 ft-lb/in) at
23.degree. C. with a 10-mil notch in a 6.4 mm (1/4-inch) thick bar
determined according to ASTM D256.
[1047] In another embodiment, certain polyesters useful in the
invention can exhibit an increase in notched Izod impact strength
when measured at 0.degree. C. of at least 3% or at least 5% or at
least 10% or at least 15% as compared to the notched Izod impact
strength when measured at -5.degree. C. with a 10-mil notch in a
1/8-inch thick bar determined according to ASTM D256. In addition,
certain other polyesters useful in the invention can also exhibit a
retention of notched Izod impact strength within plus or minus 5%
when measured at 0.degree. C. through 30.degree. C. with a 10-mil
notch in a 1/8-inch thick bar determined according to ASTM
D256.
[1048] In yet another embodiment, certain polyesters useful in the
invention can exhibit a retention in notched Izod impact strength
with a loss of no more than 70% when measured at 23.degree. C. with
a 10-mil notch in a 1/4-inch thick bar determined according to ASTM
D256 as compared to notched Izod impact strength for the same
polyester when measured at the same temperature with a 10-mil notch
in a 1/8-inch thick bar determined according to ASTM D256.
[1049] In one embodiment, the polyesters useful in the invention
can exhibit a ductile-to-brittle transition temperature of less
than 0.degree. C. based on a 10-mil notch in a 1/8-inch thick bar
as defined by ASTM D256.
[1050] In one embodiment, the polyesters useful in the invention
can exhibit at least one of the following densities as determined
using a gradient density column at 23.degree. C.: a density of less
than 1.2 g/ml at 23.degree. C.; a density of less than 1.18 g/ml at
23.degree. C.; a density of 0.8 to 1.3 g/ml at 23.degree. C.; a
density of 0.80 to 1.2 g/ml at 23.degree. C.; a density of 0.80 to
less than 1.2 g/ml at 23.degree. C.; a density of 1.0 to 1.3 g/ml
at 23.degree. C.; a density of 1.0 to 1.2 g/ml at 23.degree. C.; a
density of 1.0 to 1.1 g/ml at 23.degree. C.; a density of 1.13 to
1.3 g/ml at 23.degree. C.; a density of 1.13 to 1.2 g/ml at
23.degree. C.
[1051] In one embodiment, the polyesters useful in this invention
can be visually clear. The term "visually clear" is defined herein
as an appreciable absence of cloudiness, haziness, and/or
muddiness, when inspected visually. In another embodiment, when the
polyesters are blended with polycarbonate, including, but not
limited to, bisphenol A polycarbonates, the blends can be visually
clear.
[1052] In other embodiments of the invention, the polyesters useful
in the invention may have a yellowness index (ASTM D-1925) of less
than 50 or less than 20.
[1053] In one embodiment, the polyesters useful in the invention
and/or the polyester compositions of the invention, with or without
toners, can have color values L*, a* and b* which were determined
using a Hunter Lab Ultrascan Spectra Colorimeter manufactured by
Hunter Associates Lab Inc., Reston, Va. The color determinations
are averages of values measured on either pellets of the polyesters
or plaques or other items injection molded or extruded from them.
They are determined by the L*a*b* color system of the CIE
(International Commission on Illumination) (translated), wherein L*
represents the lightness coordinate, a* represents the red/green
coordinate, and b* represents the yellow/blue coordinate. In
certain embodiments, the b* values for the polyesters useful in the
invention can be from -10 to less than 10 and the L* values can be
from 50 to 90. In other embodiments, the b* values for the
polyesters useful in the invention can be present in one of the
following ranges: from:from -10 to 9; -10 to 8; -10 to 7; -10 to 6;
-10 to 5; -10 to 4; -10 to 3; -10 to 2; from -5 to 9; -5 to 8; -5
to 7; -5 to 6; -5 to 5; -5 to 4; -5 to 3; -5 to 2; 0 to 9; 0 to 8;
0 to 7; 0 to 6; 0 to 5; 0 to 4; 0 to 3; 0 to 2; 1 to 10; 1 to 9; 1
to 8; 1 to 7; 1 to 6; 1 to 5; 1 to 4; 1 to 3; and 1 to 2. In other
embodiments, the L* value for the polyesters useful in the
invention can be present in one of the following ranges: 50 to 60;
50 to 70; 50 to 80; 50 to 90; 60 to 70; 60 to 80; 60 to 90; 70 to
80; 79 to 90.
[1054] In some embodiments, use of the polyester compositions
useful in the invention minimizes and/or eliminates the drying step
prior to melt processing and/or thermoforming.
[1055] In one embodiment, polyesters of this invention exhibit
superior notched toughness in thick sections. Notched Izod impact
strength, as described in ASTM D256, is a common method of
measuring toughness. When tested by the Izod method, polymers can
exhibit either a complete break failure mode, where the test
specimen breaks into two distinct parts, or a partial or no break
failure mode, where the test specimen remains as one part. The
complete break failure mode is associated with low energy failure.
The partial and no break failure modes are associated with high
energy failure. A typical thickness used to measure Izod toughness
is 1/8''. At this thickness, very few polymers are believed to
exhibit a partial or no break failure mode, polycarbonate being one
notable example. When the thickness of the test specimen is
increased to 1/4'', however, no commercial amorphous materials
exhibit a partial or no break failure mode. In one embodiment,
compositions of the present example exhibit a no break failure mode
when tested in Izod using a 1/4'' thick specimen.
[1056] The polyesters useful in the invention exhibit a
ductile-to-brittle transition temperature of less than 0.degree. C.
based on a 10-mil notch in a 1/8-inch thick bar as defined by ASTM
D256.
[1057] The polyester portion of the polyester composition useful in
the invention can be made by processes known from the literature
such as, for example, by processes in homogenous solution, by
transesterification processes in the melt, and by two phase
interfacial processes. Suitable methods include the steps of
reacting one or more dicarboxylic acids with one or more glycols at
a temperature of 100.degree. C. to 315.degree. C. at a pressure of
0.1 to 760 mm Hg for a time sufficient to form a polyester. See
U.S. Pat. No. 3,772,405 for methods of producing polyesters.
[1058] In a second aspect, the invention relates to medical devices
comprising a polyester produced by a process comprising: [1059] (I)
heating a mixture comprising the monomers useful in any of the
polyesters in the invention in the presence of a catalyst at a
temperature of 150 to 240.degree. C. for a time sufficient to
produce an initial polyester; [1060] (II) heating the initial
polyester of step (I) at a temperature of 240 to 320.degree. C. for
1 to 4 hours; and [1061] (III) removing any unreacted glycols.
[1062] Suitable catalysts for use in this process include, but are
not limited to, organo-zinc or tin compounds. The use of this type
of catalyst is well known in the art. Examples of catalysts useful
in the present invention include, but are not limited to, zinc
acetate, butyltin tris-2-ethylhexanoate, dibutyltin diacetate,
and/or dibutyltin oxide. Other catalysts may include, but are not
limited to, those based on titanium, zinc, manganese, lithium,
germanium, and cobalt. Catalyst amounts can range from 10 ppm to
20,000 ppm or 10 to 10,000 ppm, or 10 to 5000 ppm or 10 to 1000 ppm
or 10 to 500 ppm, or 10 to 300 ppm or 10 to 250 based on the
catalyst metal and based on the weight of the final polymer
[1063] Typically, step (I) is carried out until 50% by weight or
more of the 2,2,4,4-tetramethyl-1,3-cyclobutanediol has been
reacted. Step (I) maybe carried out under pressure, ranging from
atmospheric pressure to 100 psig.
[1064] Typically, Step (II) and Step (III) can be conducted at the
same time. These steps can be carried out by methods known in the
art such as by placing the reaction mixture under a pressure
ranging, from 0.002 psig to atmospheric pressure, or by blowing hot
nitrogen gas over the mixture.
[1065] The invention further relates to a polyester product made by
the process described above.
[1066] The invention further relates to a polymer blend. The blend
comprises: [1067] (a) from 5 to 95 wt % of the polyesters described
above; and [1068] (b) from 5 to 95 wt % of a polymeric
component.
[1069] Suitable examples of the polymeric components include, but
are not limited to, polyamides such as nylon; other polyesters
different than those described herein; ZYTEL.RTM. from DuPont;
polystyrene; polystyrene copolymers; styrene acrylonitrile
copolymers; acrylonitrile butadiene styrene copolymers;
poly(methylmethacrylate); acrylic copolymers; poly(ether-imides)
such as ULTEM.RTM. (a poly(ether-imide) from General Electric);
polyphenylene oxides such as poly(2,6-dimethylphenylene oxide) or
poly(phenylene oxide)/polystyrene blends such as NORYL 1000.RTM. (a
blend of poly(2,6-dimethylphenylene oxide) and polystyrene resins
from General Electric); polyphenylene sulfides; polyphenylene
sulfide/sulfones; poly(ester-carbonates); polycarbonates such as
LEXAN.RTM. (a polycarbonate from General Electric); polysulfones;
polysulfone ethers; and poly(ether-ketones) of aromatic dihydroxy
compounds; or mixtures of any of the foregoing polymers. The blends
can be prepared by conventional processing techniques known in the
art, such as melt blending or solution blending. In one embodiment,
polycarbonate is not present in the polyester composition. If
polycarbonate is used in a blend in the polyester compositions of
the invention, the blends can be visually clear. The polyester
compositions useful in the invention also contemplate the exclusion
of polycarbonate as well as the inclusion of polycarbonate.
[1070] Polycarbonates useful in the invention may be prepared
according to known procedures by reacting the dihydroxyaromatic
compound with a carbonate precursor such as phosgene, a haloformate
or a carbonate ester, a molecular weight regulator, an acid
acceptor and a catalyst. Methods for preparing polycarbonates are
known in the art and are described, for example, in U.S. Pat. No.
4,452,933, which is hereby incorporated by reference herein.
[1071] Examples of suitable carbonate precursors include carbonyl
bromide, carbonyl chloride, or mixtures thereof; diphenyl
carbonate; a di(halophenyl)-carbonate, e.g.,
di(trichlorophenyl)carbonate, di(tribromophenyl)carbonate, and the
like; di(alkylphenyl)carbonate, e.g., di(tolyl)carbonate;
di(naphthyl)carbonate; di(chloronaphthyl)carbonate, or mixtures
thereof; and bis-haloformates of dihydric phenols.
[1072] Examples of suitable molecular weight regulators include,
but are not limited to, phenol, cyclohexanol, methanol, alkylated
phenols, such as octylphenol, para-tertiary-butyl-phenol, and the
like. In one embodiment, the molecular weight regulator is phenol
or an alkylated phenol.
[1073] The acid acceptor may be either an organic or an inorganic
acid acceptor. A suitable organic acid acceptor is a tertiary amine
and includes such materials as pyridine, triethylamine,
dimethylaniline, tributylamine, and the like. The inorganic acid
acceptor can be either a hydroxide, a carbonate, a bicarbonate, or
a phosphate of an alkali or alkaline earth metal.
[1074] The catalysts that can be used are those that typically aid
the polymerization of the monomer with phosgene. Suitable catalysts
include tertiary amines such as triethylamine, tripropylamine,
N,N-dimethylaniline, quaternary ammonium compounds such as, for
example, tetraethylammonium bromide, cetyl triethyl ammonium
bromide, tetra-n-heptylammonium iodide, tetra-n-propyl ammonium
bromide, tetramethyl ammonium chloride, tetra-methyl ammonium
hydroxide, tetra-n-butyl ammonium iodide, benzyltrimethyl ammonium
chloride and quaternary phosphonium compounds such as, for example,
n-butyltriphenyl phosphonium bromide and methyltriphenyl
phosphonium bromide.
[1075] The polycarbonates useful in the polyester compositions
which are useful in the invention also may be copolyestercarbonates
such as those described in U.S. Pat. Nos. 3,169,121; 3,207,814;
4,194,038; 4,156,069; 4,430,484, 4,465,820, and 4,981,898, all of
which are incorporated by reference herein.
[1076] Copolyestercarbonates useful in this invention are available
commercially. They are typically obtained by the reaction of at
least one dihydroxyaromatic compound with a mixture of phosgene and
at least one dicarboxylic acid chloride, especially isophthaloyl
chloride, terephthaloyl chloride, or both.
[1077] In addition, the polyester compositions and the polymer
blend compositions useful in the medical devices of this invention
may also contain from 0.1 to 25% by weight of the overall
composition common additives such as colorants, mold release
agents, flame retardants, plasticizers, nucleating agents,
stabilizers, including but not limited to, UV stabilizers, thermal
stabilizers, fillers, and impact modifiers. Residues of such
additives are also contemplated as part of the polyester
composition. Examples of typical commercially available impact
modifiers well known in the art and useful in this invention
include, but are not limited to, ethylene/propylene terpolymers,
styrene-based block copolymeric impact modifiers, and various
acrylic core/shell type impact modifiers.
[1078] In addition, the polyester compositions and the polymer
blend compositions containing the polyesters of this invention may
also contain from 0.01 to 25% by weight or 0.01 to 20% by weight or
0.01 to 15% by weight or 0.01 to 10% by weight or 0.01 to 5% by
weight of the total weight of the polyester composition of common
additives such as colorants, dyes, mold release agents, flame
retardants, plasticizers, nucleating agents, stabilizers, including
but not limited to, UV stabilizers, thermal stabilizers and/or
reaction products thereof, fillers, and impact modifiers. Examples
of typical commercially available impact modifiers well known in
the art and useful in this invention include, but are not limited
to, ethylene/propylene terpolymers; functionalized polyolefins,
such as those containing methyl acrylate and/or glycidyl
methacrylate; styrene-based block copolymeric impact modifiers; and
various acrylic core/shell type impact modifiers. For example, UV
additives can be incorporated into articles of manufacture through
addition to the bulk, through application of a hard coat, or
through coextrusion of a cap layer. Residues of such additives are
also contemplated as part of the polyester composition.
[1079] The polyesters of the invention can comprise at least one
chain extender. Suitable chain extenders include, but are not
limited to, multifunctional (including, but not limited to,
bifunctional) isocyanates, multifunctional epoxides, including for
example, epoxylated novolacs, and phenoxy resins. In certain
embodiments, chain extenders may be added at the end of the
polymerization process or after the polymerization process. If
added after the polymerization process, chain extenders can be
incorporated by compounding or by addition during conversion
processes such as injection molding or extrusion. The amount of
chain extender used can vary depending on the specific monomer
composition used and the physical properties desired but is
generally about 0.1 percent by weight to about 10 percent by
weight, preferably about 0.1 to about 5 percent by weight, based on
the total weight of the polyester.
[1080] Thermal stabilizers are compounds that stabilize polyesters
during polyester manufacture and/or post polymerization, including,
but not limited to, phosphorous compounds including but not limited
to phosphoric acid, phosphorous acid, phosphonic acid, phosphinic
acid, phosphonous acid, and various esters and salts thereof. These
can be present in the polyester compositions useful in the
invention. The esters can be alkyl, branched alkyl, substituted
alkyl, difunctional alkyl, alkyl ethers, aryl, and substituted
aryl. In one embodiment, the number of ester groups present in the
particular phosphorous compound can vary from zero up to the
maximum allowable based on the number of hydroxyl groups present on
the thermal stabilizer used. The term "thermal stabilizer" is
intended to include the reaction product(s) thereof. The term
"reaction product" as used in connection with the thermal
stabilizers of the invention refers to any product of a
polycondensation or esterification reaction between the thermal
stabilizer and any of the monomers used in making the polyester as
well as the product of a polycondensation or esterification
reaction between the catalyst and any other type of additive.
[1081] Reinforcing materials may be useful in the compositions of
this invention. The reinforcing materials may include, but are not
limited to, carbon filaments, silicates, mica, clay, talc, titanium
dioxide, Wollastonite, glass flakes, glass beads and fibers, and
polymeric fibers and combinations thereof. In one embodiment, the
reinforcing materials are glass, such as, fibrous glass filaments,
mixtures of glass and talc, glass and mica, and glass and polymeric
fibers.
[1082] The invention further relates to medical devices described
herein. The methods of forming the polyesters into medical devices
are well known in the art. Examples of medical devices include but
are not limited to medical bottles. These medical bottles include
but are not limited to injection blow molded bottles, injection
stretch blow molded bottles, extrusion blow molded bottles, and
extrusion stretch blow molded bottles. Methods of making bottles
include but are not limited to extrusion blow molding, extrusion
stretch blow molding, injection blow molding, and injection stretch
blow molding.
[1083] In another embodiment, the invention further relates to
medical devices comprising articles of manufacture comprising any
of the polyesters and blends described herein extruded, calendered,
and/or molded articles including but not limited to, injection
molded articles, extruded articles, cast extrusion articles,
profile extrusion articles, melt spun articles, thermoformed
articles, extrusion molded articles, injection blow molded
articles, injection stretch blow molded articles, extrusion blow
molded articles, and extrusion stretch blow molded articles. These
articles can include, but are not limited, to films, bottles
(including, but not limited to, baby bottles), containers, sheet
and/or fibers.
[1084] The methods of forming the polyesters into fibers, films,
molded articles, containers, and sheeting are well known in the
art. Examples of potential molded articles include without
limitation: medical devices such as dialysis equipment, medical
packaging, healthcare supplies, commercial foodservice products
such as food pans, steam trays, tumblers and storage boxes, baby
bottles, food processors, blender and mixer bowls, utensils, water
bottles, crisper trays, washing machine fronts, and vacuum cleaner
parts. Other potential molded articles could include, but are not
limited to, ophthalmic lenses and frames. For instance, this
material can be used to make bottles, including, but not limited
to, baby bottles, as it is clear, tough, heat resistant, and
displays good hydrolytic stability.
[1085] In another embodiment, the invention further relates to
medical devices comprising articles of manufacture comprising the
film(s) and/or sheet(s) containing polyester compositions described
herein.
[1086] The films and/or sheets useful in the present invention can
be of any thickness which would be apparent to one of ordinary
skill in the art. In one embodiment, the film(s) useful in the
invention have a thickness of no more than 40 mils. In one
embodiment, the film(s) of the invention have a thickness of no
more than 35 mils. In one embodiment, the film(s) useful in the
invention have a thickness of no more than 30 mils. In one
embodiment, the film(s) of the invention have a thickness of no
more than 25 mils. In one embodiment, the film(s) of the invention
have a thickness of no more than 20 mils.
[1087] In one embodiment, the sheet(s) of the invention have a
thickness of no less than 20 mils. In another embodiment, the
sheet(s) of the invention have a thickness of no less than 25 mils.
In another embodiment, the sheet(s) of the invention have a
thickness of no less than 30 mils. In another embodiment, the
sheet(s) of the invention have a thickness of no less than 35 mils.
In another embodiment, the sheet(s) of the invention have a
thickness of no less than 40 mils.
[1088] The invention further relates to the film(s) and/or sheet(s)
comprising the polyester compositions of the invention. The methods
of forming the polyesters into film(s) and/or sheet(s) are well
known in the art. Examples of film(s) and/or sheet(s) of the
invention including but not limited to extruded film(s) and/or
sheet(s), calendered film(s) and/or sheet(s), compression molded
film(s) and/or sheet(s), solution casted film(s) and/or sheet(s).
Methods of making film and/or sheet include but are not limited to
extrusion, calendering, compression molding, and solution
casting.
[1089] In one embodiment the present invention relates to medical
devices, such as lab-ware and components of diagnostic test kits,
that may come into contact with biological fluids or biological
systems and that have a reduced interaction with that biological
fluid or system. Medical devices include, but are not limited to,
diagnostic equipment, such tubes, bottles, bags, and other
containers; fluid handling apparatus, such as intravenous (IV)
systems including needles and hubs, cannulae, tubing, connectors
and other fixtures; blood treatment and dialysis equipment,
including dialyzers, filters, and oxygenators; anesthesia and
respiratory therapy equipment, such as masks and tubing; drug
delivery and packaging supplies, such as syringes, tubing,
transdermal patches, inhalers, bags and bottles; catheters, tubes,
and endoscopy equipment; and labware, including dishes, vials,
plates and cell culture equipment. The devices comprise a UV-cured
silicone polymer coating, which is applied to a surface of the
device so as to reduce the response of the biological fluid or
system in contact with the device. The resultant devices possess a
thin, adherent coating of silicone polymer which gives
biocompatibility. By using a coating, the advantageous properties
of the substrate material may be obtained, which may include
stiffness, clarity, favorable economics or other desirable
properties. In another embodiment the present invention relates to
a method of reducing the interaction between a medical device
comprising any of the polyesters comprising a cyclobutanediol
described above and a biological fluid or system, the method
comprising coating at least a portion of a surface of the device
with a UV-curable silicone polymer composition and exposing at
least a portion of the silicone polymer composition to ultraviolet
light to cure the composition.
[1090] The UV-curable silicone polymer composition can be applied
to nearly any substrate known in the art for use in medical
devices. Such substrates include, for example, plastics,
elastomers, metals and the like. Specific materials include
polyvinylchlorides (PVC), polycarbonates (PC), polyurethanes (PU),
polypropylenes (PP), polyethylenes (PE), silicones, polyesters,
cellulose acetates, polymethylmethacrylates (PMMA),
hydroxyethylmethacrylates, N-vinyl pyrrolidones, fluorinated
polymers such as polytetrafluoroethylene, polyamides, polystyrenes,
copolymers or mixtures of the above polymers and medical grade
metals such as steel or titanium.
[1091] Examples of UV-curable silicone polymers that can be used in
the coating composition of the invention include polymers composed
of at least 50 mole % dimethyl siloxane repeat units. Other
suitable UV-curable silicone polymers are known in the art such as
those mentioned in U.S. Pat. Nos. 4,576,999; 4,279,717; 4,421,904;
4,547,431; 4,576,999; and 4,977,198; the entire contents of which
are hereby incorporated by reference.
[1092] The coating composition may be applied by any number of
methods, including but not limited to spraying, dipping, printing,
or flow-coating. Other methods of application known in the art are
also to be considered within the scope of this invention. Further,
the polymer may be used in solution or emulsified to reduce its
viscosity for application. A diluent, if employed, may be allowed
to evaporate, and this evaporation may be facilitated by applying
energy via heat or radiation. Optionally, evaporation of all or
part of the solvent may be accomplished after a curing
operation.
[1093] Any solvent that is capable of dissolving or substantially
dissolving the silicone polymer such that its viscosity is reduced
for application may be used. Examples of such solvents include
aliphatic or aromatic hydrocarbons, such as toluene and
cyclohexane; volative silicones such as cyclomethicone; chlorinated
hydrocarbons; and esters (see, e.g., Polymer Handbook, Brandup and
Immergut, Eds., 2nd edition, page IV-253 (1975)). In addition, the
viscosity of the coatings could be decreased through
emulsification, or lowering the molecular weight of the
silicones.
[1094] The silicone polymer coating composition may further include
one or more UV curing agents to help facilitate curing of the
composition. Suitable UV curing agents may be obtained commercially
from vendors of the UV-curable silicone polymers such as General
Electric Co. Suitable UV curing agents are also known in the art
such as in U.S. Pat. Nos. 4,576,999; 4,279,717; 4,421,904;
4,547,431; 4,576,999; and 4,977,198.
[1095] Curing of the coating may be achieved by exposure to UV
radiation, which may be produced by any convenient means. The
curing time depends on a number of factors including the precise
polymer composition and the desired degree of cross-linking.
Preferably, the curing time is less than 5 seconds.
[1096] The finished coating may have a range of thicknesses, from
several nanometers up to several millimeters, preferably from 0.1
to 100 micrometers. Similarly, the substrate thickness may vary,
from about 0.001 millimeters to about 100 millimeters, preferably
from about 0.01 millimeters to about 10 millimeters.
[1097] The ability to cure using ultraviolet light rather than a
thermally cured polysiloxane is desirable in areas in which the
substrate might be sensitive to elevated temperatures. For devices
used in medical applications, this is a common concern as not all
materials can withstand elevated temperature in procedures such as
steam sterilization. For temperature-sensitive substrates, other
sterilization methods can be used that do not involve the
application of heat, such as gamma irradiation or ethylene oxide
treatment. The use of UV curing polysiloxanes according to the
present invention allows these same temperature-sensitive
substrates to be made biocompatible. By "temperature-sensitive
substrates," it is meant substrates that can irreversibly change
their characteristics (such as dimensions, shape, color,
brittleness, crystallinity, etc.) at elevated temperatures
typically employed in medical or diagnostic applications. Examples
of such substrates include polymers having relatively low
softening, melting, or glass transition temperature points.
[1098] Additionally, by crosslinking the coating using UV
radiation, patterned surfaces may be formed. In this way, selective
areas may be made to resist protein adsorption, while other areas
may be receptive to protein adsorption. By exposing selected areas
to UV light, the non-exposed, non-crosslinked areas may be
subsequently removed by various techniques, such as solvent
washing. This could produce patterned areas of relatively low and
high protein binding, for analytical tests and other
applications.
[1099] An embodiment of the present invention is further
illustrated by the following examples. It will be apparent to those
skilled in the art that various modifications and variations can be
made in the present invention without departing from the scope or
spirit of the invention. Other embodiments of the invention will be
apparent to those skilled in the art from consideration of the
specification and practice of the invention disclosed herein. It is
intended that the specification and examples be considered as
exemplary only, with a true scope and spirit of the invention being
indicated by the following claims. Moreover, all patents, patent
application (published and unpublished, foreign or domestic),
literature references or other publications noted above are
incorporated herein by reference for any disclosure pertinent to
the practice of this invention.
[1100] The following examples further illustrate how the medical
devices of the invention can be made and evaluated, and are
intended to be purely exemplary of the invention and are not
intended to limit the scope thereof. Unless indicated otherwise,
parts are parts by weight, temperature is in degrees C. or is at
room temperature, and pressure is at or near atmospheric.
EXAMPLES
Measurement Methods
[1101] The inherent viscosity of the polyesters was determined in
60/40 (wt/wt) phenol/tetrachloroethane at a concentration of 0.5
g/100 ml at 25.degree. C.
[1102] Unless stated otherwise, the glass transition temperature
(T.sub.g) was determined using a TA DSC 2920 instrument from
Thermal Analyst Instruments at a scan rate of 20.degree. C./min
according to ASTM D3418.
[1103] The glycol content and the cis/trans ratio of the
compositions were determined by proton nuclear magnetic resonance
(NMR) spectroscopy. All NMR spectra were recorded on a JEOL Eclipse
Plus 600 MHz nuclear magnetic resonance spectrometer using either
chloroform-trifluoroacetic acid (70-30 volume/volume) for polymers
or, for oligomeric samples, 60/40 (wt/wt) phenol/tetrachloroethane
with deuterated chloroform added for lock. Peak assignments for
2,2,4,4-tetramethyl-1,3-cyclobutanediol resonances were made by
comparison to model mono- and dibenzoate esters of
2,2,4,4-tetramethyl-1,3-cyclobutanediol. These model compounds
closely approximate the resonance positions found in the polymers
and oligomers.
[1104] The crystallization half-time, t1/2, was determined by
measuring the light transmission of a sample via a laser and photo
detector as a function of time on a temperature controlled hot
stage. This measurement was done by exposing the polymers to a
temperature, T.sub.max, and then cooling it to the desired
temperature. The sample was then held at the desired temperature by
a hot stage while transmission measurements were made as a function
of time. Initially, the sample was visually clear with high light
transmission and became opaque as the sample crystallized. The
crystallization half-time was recorded as the time at which the
light transmission was halfway between the initial transmission and
the final transmission. T.sub.max is defined as the temperature
required to melt the crystalline domains of the sample (if
crystalline domains are present). The T.sub.max reported in the
examples below represents the temperature at which each sample was
heated to condition the sample prior to crystallization half time
measurement. The T.sub.max temperature is dependant on composition
and is typically different for each polyester. For example, PCT may
need to be heated to some temperature greater than 290.degree. C.
to melt the crystalline domains.
[1105] Density was determined using a gradient density column at
23.degree. C.
[1106] The melt viscosity reported herein was measured by using a
Rheometrics Dynamic Analyzer (RDA II). The melt viscosity was
measured as a function of shear rate, at frequencies ranging from 1
to 400 rad/sec, at the temperatures reported. The zero shear melt
viscosity (.eta..sub.o) is the melt viscosity at zero shear rate
estimated by extrapolating the data by known models in the art.
This step is automatically performed by the Rheometrics Dynamic
Analyzer (RDA II) software.
[1107] The polymers were dried at a temperature ranging from 80 to
100.degree. C. in a vacuum oven for 24 hours and injection molded
on a Boy 22S molding machine to give 1/8.times.1/2.times.5-inch and
1/4.times.1/2.times.5-inch flexure bars. These bars were cut to a
length of 2.5 inch and notched down the 1/2 inch width with a
10-mil notch in accordance with ASTM D256. The average Izod impact
strength at 23.degree. C. was determined from measurements on 5
specimens.
[1108] In addition, 5 specimens were tested at various temperatures
using 5.degree. C. increments in order to determine the
brittle-to-ductile transition temperature. The brittle-to-ductile
transition temperature is defined as the temperature at which 50%
of the specimens fail in a brittle manner as denoted by ASTM
D256.
[1109] Color values reported herein were determined using a Hunter
Lab Ultrascan Spectra Colorimeter manufactured by Hunter Associates
Lab Inc., Reston, Va. The color determinations were averages of
values measured on either pellets of the polyesters or plaques or
other items injection molded or extruded from them. They were
determined by the L*a*b* color system of the CIE (International
Commission on Illumination) (translated), wherein L* represents the
lightness coordinate, a* represents the red/green coordinate, and
b* represents the yellow/blue coordinate.
[1110] In addition, 10-mil films were compression molded using a
Carver press at 240.degree. C.
[1111] Unless otherwise specified, the cis/trans ratio of the 1,4
cyclohexanedimethanol used in the following examples was
approximately 30/70, and could range from 35/65 to 25/75. Unless
otherwise specified, the cis/trans ratio of the
2,2,4,4-tetramethyl-1,3-cyclobutanediol used in the following
examples was approximately 50/50.
[1112] The following abbreviations apply throughout the working
examples and figures: TABLE-US-00001 TPA Terephthalic acid DMT
Dimethyl terephthalate TMCD 2,2,4,4-tetramethyl-1,3-cyclobutanediol
CHDM 1,4-cyclohexanedimethanol IV Inherent viscosity .eta..sub.o
Zero shear melt viscosity T.sub.g Glass transition temperature
T.sub.bd Brittle-to-ductile transition temperature T.sub.max
Conditioning temperature for crystallization half time
measurements
Example 1
[1113] This example illustrates that
2,2,4,4-tetramethyl-1,3-cyclobutanediol is more effective at
reducing the crystallization rate of PCT than ethylene glycol or
isophthalic acid. In addition, this example illustrates the
benefits of 2,2,4,4-tetramethyl-1,3-cyclobutanediol on the glass
transition temperature and density.
[1114] A variety of copolyesters were prepared as described below.
These copolyesters were all made with 200 ppm dibutyl tin oxide as
the catalyst in order to minimize the effect of catalyst type and
concentration on nucleation during crystallization studies. The
cis/trans ratio of the 1,4-cyclohexanedimethanol was 31/69 while
the cis/trans ratio of the 2,2,4,4-tetramethyl-1,3-cyclobutanediol
is reported in Table 1.
[1115] For purposes of this example, the samples had sufficiently
similar inherent viscosities thereby effectively eliminating this
as a variable in the crystallization rate measurements.
[1116] Crystallization half-time measurements from the melt were
made at temperatures from 140 to 200.degree. C. at 10.degree. C.
increments and are reported in Table 1. The fastest crystallization
half-time for each sample was taken as the minimum value of
crystallization half-time as a function of temperature, typically
occurring around 170 to 180.degree. C. The fastest crystallization
half-times for the samples are plotted in FIG. 1 as a function of
mole % comonomer modification to PCT.
[1117] The data shows that 2,2,4,4-tetramethyl-1,3-cyclobutanediol
is more effective than ethylene glycol and isophthalic acid at
decreasing the crystallization rate (i.e., increasing the
crystallization half-time). In addition,
2,2,4,4-tetramethyl-1,3-cyclobutanediol increases T.sub.g and
lowers density. TABLE-US-00002 TABLE 1 Crystallization Half-times
(min) at at at at at at at Comonomer IV Density T.sub.g T.sub.max
140.degree. C. 150.degree. C. 160.degree. C. 170.degree. C.
180.degree. C. 190.degree. C. 200.degree. C. Example (mol %).sup.1
(dl/g) (g/ml) (.degree. C.) (.degree. C.) (min) (min) (min) (min)
(min) (min) (min) 1A 20.2% A.sup.2 0.630 1.198 87.5 290 2.7 2.1 1.3
1.2 0.9 1.1 1.5 1B 19.8% B 0.713 1.219 87.7 290 2.3 2.5 1.7 1.4 1.3
1.4 1.7 1C 20.0% C 0.731 1.188 100.5 290 >180 >60 35.0 23.3
21.7 23.3 25.2 1D 40.2% A.sup.2 0.674 1.198 81.2 260 18.7 20.0 21.3
25.0 34.0 59.9 96.1 1E 34.5% B 0.644 1.234 82.1 260 8.5 8.2 7.3 7.3
8.3 10.0 11.4 1F 40.1% C 0.653 1.172 122.0 260 >10 days >5
days >5 days 19204 >5 days >5 days >5 days 1G 14.3% D
0.646.sup.3 1.188 103.0 290 55.0 28.8 11.6 6.8 4.8 5.0 5.5 1H 15.0%
E 0.728.sup.4 1.189 99.0 290 25.4 17.1 8.1 5.9 4.3 2.7 5.1
.sup.1The balance of the diol component of the polyesters in Table
1 is 1,4-cyclohexanedimethanol; and the balance of the dicarboxylic
acid component of the polyesters in Table 1 is dimethyl
terephthalate; if the dicarboxylic acid is not described, it is 100
mole % dimethyl terephthalate. .sup.2100 mole %
1,4-cyclohexanedimethanol. .sup.3A film was pressed from the ground
polyester of Example 1G at 240.degree. C. The resulting film had an
inherent viscosity value of 0.575 dL/g. .sup.4A film was pressed
from the ground polyester of Example 1H at 240.degree. C. The
resulting film had an inherent viscosity value of 0.0.652 dL/g.
where: A is Isophthalic Acid B is Ethylene Glycol C is
2,2,4,4-Tetramethyl-1,3-cyclobutanediol (approx. 50/50 cis/trans) D
is 2,2,4,4-Tetramethyl-1,3-cyclobutanediol (98/2 cis/trans) E is
2,2,4,4-Tetramethyl-1,3-cyclobutanediol (5/95 cis/trans)
[1118] As shown in Table 1 and FIG. 1,
2,2,4,4-tetramethyl-1,3-cyclobutanediol is more effective than
other comonomers, such ethylene glycol and isophthalic acid, at
increasing the crystallization half-time, i.e., the time required
for a polymer to reach half of its maximum crystallinity. By
decreasing the crystallization rate of PCT (increasing the
crystallization half-time), amorphous articles based on
2,2,4,4-tetramethyl-1,3-cyclobutanediol-modified PCT as described
herein may be fabricated by methods known in the art. As shown in
Table 1, these materials can exhibit higher glass transition
temperatures and lower densities than other modified PCT
copolyesters.
[1119] Preparation of the polyesters shown on Table 1 is described
below.
Example 1A
[1120] This example illustrates the preparation of a copolyester
with a target composition of 80 mol % dimethyl terephthalate
residues, 20 mol % dimethyl isophthalate residues, and 100 mol %
1,4-cyclohexanedimethanol residues (28/72 cis/trans).
[1121] A mixture of 56.63 g of dimethyl terephthalate, 55.2 g of
1,4-cyclohexanedimethanol, 14.16 g of dimethyl isophthalate, and
0.0419 g of dibutyl tin oxide was placed in a 500-milliliter flask
equipped with an inlet for nitrogen, a metal stirrer, and a short
distillation column. The flask was placed in a Wood's metal bath
already heated to 210.degree. C. The stirring speed was set to 200
RPM throughout the experiment. The contents of the flask were
heated at 210.degree. C. for 5 minutes and then the temperature was
gradually increased to 290.degree. C. over 30 minutes. The reaction
mixture was held at 290.degree. C. for 60 minutes and then vacuum
was gradually applied over the next 5 minutes until the pressure
inside the flask reached 100 mm of Hg. The pressure inside the
flask was further reduced to 0.3 mm of Hg over the next 5 minutes.
A pressure of 0.3 mm of Hg was maintained for a total time of 90
minutes to remove excess unreacted diols. A high melt viscosity,
visually clear and colorless polymer was obtained with a glass
transition temperature of 87.5.degree. C. and an inherent viscosity
of 0.63 dL/g. NMR analysis showed that the polymer was composed of
100 mol % 1,4-cyclohexanedimethanol residues and 20.2 mol %
dimethyl isophthalate residues.
Example 1B
[1122] This example illustrates the preparation of a copolyester
with a target composition of 100 mol % dimethyl terephthalate
residues, 20 mol % ethylene glycol residues, and 80 mol %
1,4-cyclohexanedimethanol residues (32/68 cis/trans).
[1123] A mixture of 77.68 g of dimethyl terephthalate, 50.77 g of
1,4-cyclohexanedimethanol, 27.81 g of ethylene glycol, and 0.0433 g
of dibutyl tin oxide was placed in a 500-milliliter flask equipped
with an inlet for nitrogen, a metal stirrer, and a short
distillation column. The flask was placed in a Wood's metal bath
already heated to 200.degree. C. The stirring speed was set to 200
RPM throughout the experiment. The contents of the flask were
heated at 200.degree. C. for 60 minutes and then the temperature
was gradually increased to 210.degree. C. over 5 minutes. The
reaction mixture was held at 210.degree. C. for 120 minutes and
then heated up to 280.degree. C. in 30 minutes. Once at 280.degree.
C., vacuum was gradually applied over the next 5 minutes until the
pressure inside the flask reached 100 mm of Hg. The pressure inside
the flask was further reduced to 0.3 mm of Hg over the next 10
minutes. A pressure of 0.3 mm of Hg was maintained for a total time
of 90 minutes to remove excess unreacted diols. A high melt
viscosity, visually clear and colorless polymer was obtained with a
glass transition temperature of 87.7.degree. C. and an inherent
viscosity of 0.71 dL/g. NMR analysis showed that the polymer was
composed of 19.8 mol % ethylene glycol residues.
Example 1C
[1124] This example illustrates the preparation of a copolyester
with a target composition of 100 mol % dimethyl terephthalate
residues, 20 mol % 2,2,4,4-tetramethyl-1,3-cyclobutanediol
residues, and 80 mol % 1,4-cyclohexanedimethanol residues (31/69
cis/trans).
[1125] A mixture of 77.68 g of dimethyl terephthalate, 48.46 g of
1,4-cyclohexanedimethanol, 17.86 g of
2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 0.046 g of dibutyl tin
oxide was placed in a 500-milliliter flask equipped with an inlet
for nitrogen, a metal stirrer, and a short distillation column.
This polyester was prepared in a manner similar to that described
in Example 1A. A high melt viscosity, visually clear and colorless
polymer was obtained with a glass transition temperature of
100.5.degree. C. and an inherent viscosity of 0.73 dL/g. NMR
analysis showed that the polymer was composed of 80.5 mol %
1,4-cyclohexanedimethanol residues and 19.5 mol %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.
Example 1D
[1126] This example illustrates the preparation of a copolyester
with a target composition of 100 mol % dimethyl terephthalate
residues, 40 mol % dimethyl isophthalate residues, and 100 mol %
1,4-cyclohexanedimethanol residues (28/72 cis/trans).
[1127] A mixture of 42.83 g of dimethyl terephthalate, 55.26 g of
1,4-cyclohexanedimethanol, 28.45 g of dimethyl isophthalate, and
0.0419 g of dibutyl tin oxide was placed in a 500-milliliter flask
equipped with an inlet for nitrogen, a metal stirrer, and a short
distillation column. The flask was placed in a Wood's metal bath
already heated to 210.degree. C. The stirring speed was set to 200
RPM throughout the experiment. The contents of the flask were
heated at 210.degree. C. for 5 minutes and then the temperature was
gradually increased to 290.degree. C. over 30 minutes. The reaction
mixture was held at 290.degree. C. for 60 minutes and then vacuum
was gradually applied over the next 5 minutes until the pressure
inside the flask reached 100 mm of Hg. The pressure inside the
flask was further reduced to 0.3 mm of Hg over the next 5 minutes.
A pressure of 0.3 mm of Hg was maintained for a total time of 90
minutes to remove excess unreacted diols. A high melt viscosity,
visually clear and colorless polymer was obtained with a glass
transition temperature of 81.2.degree. C. and an inherent viscosity
of 0.67 dL/g. NMR analysis showed that the polymer was composed of
100 mol % 1,4-cyclohexanedimethanol residues and 40.2 mol %
dimethyl isophthalate residues.
Example 1E
[1128] This example illustrates the preparation of a copolyester
with a target composition of 100 mol % dimethyl terephthalate
residues, 40 mol % ethylene glycol residues, and 60 mol %
1,4-cyclohexanedimethanol residues (31/69 cis/trans).
[1129] A mixture of 81.3 g of dimethyl terephthalate, 42.85 g of
1,4-cyclohexanedimethanol, 34.44 g of ethylene glycol, and 0.0419 g
of dibutyl tin oxide was placed in a 500-milliliter flask equipped
with an inlet for nitrogen, a metal stirrer, and a short
distillation column. The flask was placed in a Wood's metal bath
already heated to 200.degree. C. The stirring speed was set to 200
RPM throughout the experiment. The contents of the flask were
heated at 200.degree. C. for 60 minutes and then the temperature
was gradually increased to 210.degree. C. over 5 minutes. The
reaction mixture was held at 210.degree. C. for 120 minutes and
then heated up to 280.degree. C. in 30 minutes. Once at 280.degree.
C., vacuum was gradually applied over the next 5 minutes until the
pressure inside the flask reached 100 mm of Hg. The pressure inside
the flask was further reduced to 0.3 mm of Hg over the next 10
minutes. A pressure of 0.3 mm of Hg was maintained for a total time
of 90 minutes to remove excess unreacted diols. A high melt
viscosity, visually clear and colorless polymer was obtained with a
glass transition temperature of 82.1.degree. C. and an inherent
viscosity of 0.64 dL/g. NMR analysis showed that the polymer was
composed of 34.5 mol % ethylene glycol residues.
Example 1F
[1130] This example illustrates the preparation of a copolyester
with a target composition of 100 mol % dimethyl terephthalate
residues, 40 mol % 2,2,4,4-tetramethyl-1,3-cyclobutanediol
residues, and 60 mol % 1,4-cyclohexanedimethanol residues (31/69
cis/trans).
[1131] A mixture of 77.4 g of dimethyl terephthalate, 36.9 g of
1,4-cyclohexanedimethanol, 32.5 g of
2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 0.046 g of dibutyl tin
oxide was placed in a 500-milliliter flask equipped with an inlet
for nitrogen, a metal stirrer, and a short distillation column. The
flask was placed in a Wood's metal bath already heated to
210.degree. C. The stirring speed was set to 200 RPM throughout the
experiment. The contents of the flask were heated at 210.degree. C.
for 3 minutes and then the temperature was gradually increased to
260.degree. C. over 30 minutes. The reaction mixture was held at
260.degree. C. for 120 minutes and then heated up to 290.degree. C.
in 30 minutes. Once at 290.degree. C., vacuum was gradually applied
over the next 5 minutes until the pressure inside the flask reached
100 mm of Hg. The pressure inside the flask was further reduced to
0.3 mm of Hg over the next 5 minutes. A pressure of 0.3 mm of Hg
was maintained for a total time of 90 minutes to remove excess
unreacted diols. A high melt viscosity, visually clear and
colorless polymer was obtained with a glass transition temperature
of 122.degree. C. and an inherent viscosity of 0.65 dL/g. NMR
analysis showed that the polymer was composed of 59.9 mol %
1,4-cyclohexanedimethanol residues and 40.1 mol %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.
Example 1G
[1132] This example illustrates the preparation of a copolyester
with a target composition of 100 mol % dimethyl terephthalate
residues, 20 mol % 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues
(98/2 cis/trans), and 80 mol % 1,4-cyclohexanedimethanol residues
(31/69 cis/trans).
[1133] A mixture of 77.68 g of dimethyl terephthalate, 48.46 g of
1,4-cyclohexanedimethanol, 20.77 g of
2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 0.046 g of dibutyl tin
oxide was placed in a 500-milliliter flask equipped with an inlet
for nitrogen, a metal stirrer, and a short distillation column. The
flask was placed in a Wood's metal bath already heated to
210.degree. C. The stirring speed was set to 200 RPM throughout the
experiment. The contents of the flask were heated at 210.degree. C.
for 3 minutes and then the temperature was gradually increased to
260.degree. C. over 30 minutes. The reaction mixture was held at
260.degree. C. for 120 minutes and then heated up to 290.degree. C.
in 30 minutes. Once at 290.degree. C., vacuum was gradually applied
over the next 5 minutes until the pressure inside the flask reached
100 mm of Hg and the stirring speed was also reduced to 100 RPM.
The pressure inside the flask was further reduced to 0.3 mm of Hg
over the next 5 minutes and the stirring speed was reduced to 50
RPM. A pressure of 0.3 mm of Hg was maintained for a total time of
60 minutes to remove excess unreacted diols. A high melt viscosity,
visually clear and colorless polymer was obtained with a glass
transition temperature of 103.degree. C. and an inherent viscosity
of 0.65 dL/g. NMR analysis showed that the polymer was composed of
85.7 mol % 1,4-cyclohexanedimethanol residues and 14.3 mol %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.
Example 1H
[1134] This example illustrates the preparation of a copolyester
with a target composition of 100 mol % dimethyl terephthalate
residues, 20 mol % 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues
(5/95 cis/trans), and 80 mol % 1,4-cyclohexanedimethanol residues
(31/69 cis/trans).
[1135] A mixture of 77.68 g of dimethyl terephthalate, 48.46 g of
1,4-cyclohexanedimethanol, 20.77 g of
2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 0.046 g of dibutyl tin
oxide was placed in a 500-milliliter flask equipped with an inlet
for nitrogen, a metal stirrer, and a short distillation column. The
flask was placed in a Wood's metal bath already heated to
210.degree. C. The stirring speed was set to 200 RPM at the
beginning of the experiment. The contents of the flask were heated
at 210.degree. C. for 3 minutes and then the temperature was
gradually increased to 260.degree. C. over 30 minutes. The reaction
mixture was held at 260.degree. C. for 120 minutes and then heated
up to 290.degree. C. in 30 minutes. Once at 290.degree. C., vacuum
was gradually applied over the next 5 minutes with a set point of
100 mm of Hg and the stirring speed was also reduced to 100 RPM.
The pressure inside the flask was further reduced to a set point of
0.3 mm of Hg over the next 5 minutes and the stirring speed was
reduced to 50 RPM. This pressure was maintained for a total time of
60 minutes to remove excess unreacted diols. It was noted that the
vacuum system failed to reach the set point mentioned above, but
produced enough vacuum to produce a high melt viscosity, visually
clear and colorless polymer with a glass transition temperature of
99.degree. C. and an inherent viscosity of 0.73 dL/g. NMR analysis
showed that the polymer was composed of 85 mol %
1,4-cyclohexanedimethanol residues and 15 mol %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.
Example 2
[1136] This example illustrates that
2,2,4,4-tetramethyl-1,3-cyclobutanediol improves the toughness of
PCT-based copolyesters (polyesters containing terephthalic acid and
1,4-cyclohexanedimethanol).
[1137] Copolyesters based on
2,2,4,4-tetramethyl-1,3-cyclobutanediol were prepared as described
below. The cis/trans ratio of the 1,4-cyclohexanedimethanol was
approximately 31/69 for all samples. Copolyesters based on ethylene
glycol and 1,4-cyclohexanedimethanol were commercial polyesters.
The copolyester of Example 2A (Eastar PCTG 5445) was obtained from
Eastman Chemical Co. The copolyester of Example 2B was obtained
from Eastman Chemical Co. under the trade name Spectar. Example 2C
and Example 2D were prepared on a pilot plant scale (each a 15-lb
batch) following an adaptation of the procedure described in
Example 1A and having the inherent viscosities and glass transition
temperatures described in Table 2 below. Example 2C was prepared
with a target tin amount of 300 ppm (Dibutyltin Oxide). The final
product contained 295 ppm tin. The color values for the polyester
of Example 2C were L*=77.11; a*=-1.50; and b*=5.79. Example 2D was
prepared with a target tin amount of 300 ppm (Dibutyltin Oxide).
The final product contained 307 ppm tin. The color values for the
polyester of Example 2D were L*=66.72; a*=-1.22; and b*=16.28.
[1138] Materials were injection molded into bars and subsequently
notched for Izod testing. The notched Izod impact strengths were
obtained as a function of temperature and are also reported in
Table 2.
[1139] For a given sample, the Izod impact strength undergoes a
major transition in a short temperature span. For instance, the
Izod impact strength of a copolyester based on 38 mol % ethylene
glycol undergoes this transition between 15 and 20.degree. C. This
transition temperature is associated with a change in failure mode;
brittle/low energy failures at lower temperatures and ductile/high
energy failures at higher temperatures. The transition temperature
is denoted as the brittle-to-ductile transition temperature,
T.sub.bd, and is a measure of toughness. T.sub.bd is reported in
Table 2 and plotted against mol % comonomer in FIG. 2.
[1140] The data shows that adding
2,2,4,4-tetramethyl-1,3-cyclobutanediol to PCT lowers T.sub.bd and
improves the toughness, as compared to ethylene glycol, which
increases T.sub.bd of PCT. TABLE-US-00003 TABLE 2 Notched Izod
Impact Energy (ft-lb/in) Ex- Comonomer IV T.sub.g T.sub.bd at at at
at at at at at at ample (mol %).sup.1 (dl/g) (.degree. C.)
(.degree. C.) -20.degree. C. -15.degree. C. -10.degree. C.
-5.degree. C. at 0.degree. C. at 5.degree. C. 10.degree. C.
15.degree. C. 20.degree. C. 25.degree. C. 30.degree. C. 2A 38.0% B
0.68 86 18 NA NA NA 1.5 NA NA 1.5 1.5 32 32 NA 2B 69.0% B 0.69 82
26 NA NA NA NA NA NA 2.1 NA 2.4 13.7 28.7 2C 22.0% C 0.66 106 -5
1.5 NA 12 23 23 NA 23 NA NA NA NA 2D 42.8% C 0.60 133 -12 2.5 2.5
11 NA 14 NA NA NA NA NA NA .sup.1The balance of the glycol
component of the polyesters in the Table is
1,4-cyclohexanedimethanol. All polymers were prepared from 100 mole
% dimethyl terephthalate. NA = Not available. where: B is Ethylene
glycol C is 2,2,4,4-Tetramethyl-1,3-cyclobutanediol (50/50
cis/trans)
Example 3
[1141] This example illustrates that
2,2,4,4-tetramethyl-1,3-cyclobutanediol can improve the toughness
of PCT-based copolyesters (polyesters containing terephthalic acid
and 1,4-cyclohexanedimethanol). Polyesters prepared in this example
comprise from 15 to 25 mol % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.
[1142] Copolyesters based on dimethyl terephthalate,
2,2,4,4-tetramethyl-1,3-cyclobutanediol, and
1,4-cyclohexanedimethanol were prepared as described below, having
the composition and properties shown on Table 3. The balance up to
100 mol % of the diol component of the polyesters in Table 3 was
1,4-cyclohexanedimethanol (31/69 cis/trans).
[1143] Materials were injection molded into both 3.2 mm and 6.4 mm
thick bars and subsequently notched for Izod impact testing. The
notched Izod impact strengths were obtained at 23.degree. C. and
are reported in Table 3. Density, Tg, and crystallization halftime
were measured on the molded bars. Melt viscosity was measured on
pellets at 290.degree. C. TABLE-US-00004 TABLE 3 Compilation of
various properties for certain polyesters useful in the invention
Notched Notched Izod of Izod of 3.2 mm 6.4 mm Melt thick thick
Crystallization Viscosity Pellet Molded bars at bars at Specific
Halftime from at 1 rad/sec TMCD % cis IV Bar IV 23.degree. C.
23.degree. C. Gravity Tg melt at 170.degree. C. at 290.degree. C.
Example mole % TMCD (dl/g) (dl/g) (J/m) (J/m) (g/mL) (.degree. C.)
(min) (Poise) A 15 48.8 0.736 0.707 1069 878 1.184 104 15 5649 B 18
NA 0.728 0.715 980 1039 1.183 108 22 6621 C 20 NA 0.706 0.696 1006
1130 1.182 106 52 6321 D 22 NA 0.732 0.703 959 988 1.178 108 63
7161 E 21 NA 0.715 0.692 932 482 1.179 110 56 6162 F 24 NA 0.708
0.677 976 812 1.180 109 58 6282 G 23 NA 0.650 0.610 647 270 1.182
107 46 3172 H 23 47.9 0.590 0.549 769 274 1.181 106 47 1736 I 23
48.1 0.531 0.516 696 352 1.182 105 19 1292 J 23 47.8 0.364 NA NA NA
NA 98 NA 167 NA = Not available.
Example 3A
[1144] 21.24 lb (49.71 gram-mol) dimethyl terephthalate, 14.34 lb
(45.21 gram-mol) 1,4-cyclohexanedimethanol, and 4.58 lb (14.44
gram-mol) 2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted
together in the presence of 200 ppm of the catalyst butyltin
tris(2-ethylhexanoate). The reaction was carried out under a
nitrogen gas purge in an 18-gallon stainless steel pressure vessel
fitted with a condensing column, a vacuum system, and a
HELICONE-type agitator. With the agitator running at 25 RPM, the
reaction mixture temperature was increased to 250.degree. C. and
the pressure was increased to 20 psig. The reaction mixture was
held for 2 hours at 250.degree. C. and at a pressure of 20 psig.
The pressure was then decreased to 0 psig at a rate of 3
psig/minute. The temperature of the reaction mixture was then
increased to 270.degree. C. and the pressure was decreased to 90 mm
of Hg. After a 1 hour hold time at 270.degree. C. and 90 mm of Hg,
the agitator speed was decreased to 15 RPM, the reaction mixture
temperature was increased to 290.degree. C., and the pressure was
decreased to <1 mm of Hg. The reaction mixture was held at
290.degree. C. and at a pressure of <1 mm of Hg until the power
draw to the agitator no longer increased (70 minutes). The pressure
of the pressure vessel was then increased to 1 atmosphere using
nitrogen gas. The molten polymer was then extruded from the
pressure vessel. The cooled, extruded polymer was ground to pass a
6-mm screen. The polymer had an inherent viscosity of 0.736 dL/g
and a Tg of 104.degree. C. NMR analysis showed that the polymer was
composed of 85.4 mol % 1,4-cyclohexane-dimethanol residues and 14.6
mol % 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer
had color values of: L*=78.20, a*=-1.62, and b*=6.23.
Example 3B to Example 3D
[1145] The polyesters described in Example 3B to Example 3D were
prepared following a procedure similar to the one described for
Example 3A. The composition and properties of these polyesters are
shown in Table 3.
Example 3E
[1146] 21.24 lb (49.71 gram-mol) dimethyl terephthalate, 12.61 lb
(39.77 gram-mol) 1,4-cyclohexanedimethanol, and 6.30 lb (19.88
gram-mol) 2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted
together in the presence of 200 ppm of the catalyst butyltin
tris(2-ethylhexanoate). The reaction was carried out under a
nitrogen gas purge in an 18-gallon stainless steel pressure vessel
fitted with a condensing column, a vacuum system, and a
HELICONE-type agitator. With the agitator running at 25 RPM, the
reaction mixture temperature was increased to 250.degree. C. and
the pressure was increased to 20 psig. The reaction mixture was
held for 2 hours at 250.degree. C. and 20 psig pressure. The
pressure was then decreased to 0 psig at a rate of 3 psig/minute.
The temperature of the reaction mixture was then increased to
270.degree. C. and the pressure was decreased to 90 mm of Hg. After
a 1 hour hold time at 270.degree. C. and 90 mm of Hg, the agitator
speed was decreased to 15 RPM, the reaction mixture temperature was
increased to 290.degree. C., and the pressure was decreased to
<1 mm of Hg. The reaction mixture was held at 290.degree. C. and
at a pressure of <1 mm of Hg for 60 minutes. The pressure of the
pressure vessel was then increased to 1 atmosphere using nitrogen
gas. The molten polymer was then extruded from the pressure vessel.
The cooled, extruded polymer was ground to pass a 6-mm screen. The
polymer had an inherent viscosity of 0.715 dL/g and a Tg of
110.degree. C. X-ray analysis showed that the polyester had 223 ppm
tin. NMR analysis showed that the polymer was composed of 78.6 mol
% 1,4-cyclohexane-dimethanol residues and 21.4 mol %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer had
color values of: L*=76.45, a*=-1.65, and b*=6.47.
Example 3F
[1147] The polyester described in Example 3F was prepared following
a procedure similar to the one described for Example 3A. The
composition and properties of this polyester are shown in Table
3.
Example 3H
[1148] 21.24 lb (49.71 gram-mol) dimethyl terephthalate, 12.61 lb
(39.77 gram-mol) 1,4-cyclohexanedimethanol, and 6.30 lb (19.88
gram-mol) 2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted
together in the presence of 200 ppm of the catalyst butyltin
tris(2-ethylhexanoate). The reaction was carried out under a
nitrogen gas purge in an 18-gallon stainless steel pressure vessel
fitted with a condensing column, a vacuum system, and a
HELICONE-type agitator. With the agitator running at 25 RPM, the
reaction mixture temperature was increased to 250.degree. C. and
the pressure was increased to 20 psig. The reaction mixture was
held for 2 hours at 250.degree. C. and 20 psig pressure. The
pressure was then decreased to 0 psig at a rate of 3 psig/minute.
The temperature of the reaction mixture was then increased to
270.degree. C. and the pressure was decreased to 90 mm of Hg. After
a 1 hour hold time at 270.degree. C. and 90 mm of Hg, the agitator
speed was decreased to 15 RPM, the reaction mixture temperature was
increased to 290.degree. C., and the pressure was decreased to
<1 mm of Hg. The reaction mixture was held at 290.degree. C. and
at a pressure of <1 mm of Hg for 12 minutes. The pressure of the
pressure vessel was then increased to 1 atmosphere using nitrogen
gas. The molten polymer was then extruded from the pressure vessel.
The cooled, extruded polymer was ground to pass a 6-mm screen. The
polymer had an inherent viscosity of 0.590 dL/g and a Tg of
106.degree. C. NMR analysis showed that the polymer was composed of
77.1 mol % 1,4-cyclohexane-dimethanol residues and 22.9 mol %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer had
color values of: L*=83.27, a*=-1.34, and b*=5.08.
Example 3I
[1149] 21.24 lb (49.71 gram-mol) dimethyl terephthalate, 12.61 lb
(39.77 gram-mol) 1,4-cyclohexanedimethanol, and 6.30 lb (19.88
gram-mol) 2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted
together in the presence of 200 ppm of the catalyst butyltin
tris(2-ethylhexanoate). The reaction was carried out under a
nitrogen gas purge in an 18-gallon stainless steel pressure vessel
fitted with a condensing column, a vacuum system, and a
HELICONE-type agitator. With the agitator running at 25 RPM, the
reaction mixture temperature was increased to 250.degree. C. and
the pressure was increased to 20 psig. The reaction mixture was
held for 2 hours at 250.degree. C. and 20 psig pressure. The
pressure was then decreased to 0 psig at a rate of 3 psig/minute.
The temperature of the reaction mixture was then increased to
270.degree. C. and the pressure was decreased to 90 mm of Hg. After
a 1 hour hold time at 270.degree. C. and 90 mm of Hg, the agitator
speed was decreased to 15 RPM, the reaction mixture temperature was
increased to 290.degree. C., and the pressure was decreased to 4 mm
of Hg. The reaction mixture was held at 290.degree. C. and at a
pressure of 4 mm of Hg for 30 minutes. The pressure of the pressure
vessel was then increased to 1 atmosphere using nitrogen gas. The
molten polymer was then extruded from the pressure vessel. The
cooled, extruded polymer was ground to pass a 6-mm screen. The
polymer had an inherent viscosity of 0.531 dL/g and a Tg of
105.degree. C. NMR analysis showed that the polymer was composed of
76.9 mol % 1,4-cyclohexane-dimethanol residues and 23.1 mol %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer had
color values of: L*=80.42, a*=-1.28, and b*=5.13.
Example 3J
[1150] 21.24 lb (49.71 gram-mol) dimethyl terephthalate, 12.61 lb
(39.77 gram-mol) 1,4-cyclohexanedimethanol, and 6.30 lb (19.88
gram-mol) 2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted
together in the presence of 200 ppm of the catalyst butyltin
tris(2-ethylhexanoate). The reaction was carried out under a
nitrogen gas purge in an 18-gallon stainless steel pressure vessel
fitted with a condensing column, a vacuum system, and a
HELICONE-type agitator. With the agitator running at 25 RPM, the
reaction mixture temperature was increased to 250.degree. C. and
the pressure was increased to 20 psig. The reaction mixture was
held for 2 hours at 250.degree. C. and 20 psig pressure. The
pressure was then decreased to 0 psig at a rate of 3 psig/minute.
The temperature of the reaction mixture was then increased to
270.degree. C. and the pressure was decreased to 90 mm of Hg. After
a 1 hour hold time at 270.degree. C. and 90 mm of Hg, the agitator
speed was decreased to 15 RPM, the reaction mixture temperature was
increased to 290.degree. C., and the pressure was decreased to 4 mm
of Hg. When the reaction mixture temperature was 290.degree. C. and
the pressure was 4 mm of Hg, the pressure of the pressure vessel
was immediately increased to 1 atmosphere using nitrogen gas. The
molten polymer was then extruded from the pressure vessel. The
cooled, extruded polymer was ground to pass a 6-mm screen. The
polymer had an inherent viscosity of 0.364 dL/g and a Tg of
98.degree. C. NMR analysis showed that the polymer was composed of
77.5 mol % 1,4-cyclohexane-dimethanol residues and 22.5 mol %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer had
color values of: L*=77.20, a*=-1.47, and b*=4.62.
Example 4
[1151] This example illustrates that
2,2,4,4-tetramethyl-1,3-cyclobutanediol can improve the toughness
of PCT-based copolyesters (polyesters containing terephthalic acid
and 1,4-cyclohexanedimethanol). Polyesters prepared in this example
fall comprise more than 25 to less than 40 mol % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.
[1152] Copolyesters based on dimethyl terephthalate,
2,2,4,4-tetramethyl-1,3-cyclobutanediol, and
1,4-cyclohexanedimethanol (31/69 cis/trans) were prepared as
described below, having the composition and properties shown on
Table 4. The balance up to 100 mol % of the diol component of the
polyesters in Table 4 was 1,4-cyclohexanedimethanol (31/69
cis/trans).
[1153] Materials were injection molded into both 3.2 mm and 6.4 mm
thick bars and subsequently notched for Izod impact testing. The
notched Izod impact strengths were obtained at 23.degree. C. and
are reported in Table 4. Density, Tg, and crystallization halftime
were measured on the molded bars. Melt viscosity was measured on
pellets at 290.degree. C. TABLE-US-00005 TABLE 4 Compilation of
various properties for certain polyesters useful in the invention
Notched Notched Izod of Izod of 3.2 mm 6.4 mm Melt thick thick
Crystallization Viscosity Pellet Molded bars at bars at Specific
Halftime from at 1 rad/sec TMCD % cis IV Bar IV 23.degree. C.
23.degree. C. Gravity Tg melt at 170.degree. C. at 290.degree. C.
Example mole % TMCD (dl/g) (dl/g) (J/m) (J/m) (g/mL) (.degree. C.)
(min) (Poise) A 27 47.8 0.714 0.678 877 878 1.178 113 280 8312 B 31
NA 0.667 0.641 807 789 1.174 116 600 6592 NA = Not available.
Example 4A
[1154] 21.24 lb (49.71 gram-mol) dimethyl terephthalate, 11.82 lb
(37.28 gram-mol) 1,4-cyclohexanedimethanol, and 6.90 lb (21.77
gram-mol) 2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted
together in the presence of 200 ppm of the catalyst butyltin
tris(2-ethylhexanoate). The reaction was carried out under a
nitrogen gas purge in an 18-gallon stainless steel pressure vessel
fitted with a condensing column, a vacuum system, and a
HELICONE-type agitator. With the agitator running at 25 RPM, the
reaction mixture temperature was increased to 250.degree. C. and
the pressure was increased to 20 psig. The reaction mixture was
held for 2 hours at 250.degree. C. and 20 psig pressure. The
pressure was then decreased to 0 psig at a rate of 3 psig/minute.
The temperature of the reaction mixture was then increased to
270.degree. C. and the pressure was decreased to 90 mm of Hg. After
a 1 hour hold time at 270.degree. C. and 90 mm of Hg, the agitator
speed was decreased to 15 RPM, the reaction mixture temperature was
increased to 290.degree. C., and the pressure was decreased to
<1 mm of Hg. The reaction mixture was held at 290.degree. C. and
at a pressure of <1 mm of Hg until the power draw to the
agitator no longer increased (50 minutes). The pressure of the
pressure vessel was then increased to 1 atmosphere using nitrogen
gas. The molten polymer was then extruded from the pressure vessel.
The cooled, extruded polymer was ground to pass a 6-mm screen. The
polymer had an inherent viscosity of 0.714 dL/g and a Tg of
113.degree. C. NMR analysis showed that the polymer was composed of
73.3 mol % 1,4-cyclohexane-dimethanol residues and 26.7 mol %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.
Example 4B
[1155] The polyester of Example 4B was prepared following a
procedure similar to the one described for Example 4A. The
composition and properties of this polyester are shown in Table
4.
Example 5
[1156] This example illustrates that
2,2,4,4-tetramethyl-1,3-cyclobutanediol can improve the toughness
of PCT-based copolyesters (polyesters containing terephthalic acid
and 1,4-cyclohexanedimethanol). Polyesters prepared in this example
comprise 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues in an
amount of 40 mol % or greater.
[1157] Copolyesters based on dimethyl terephthalate,
2,2,4,4-tetramethyl-1,3-cyclobutanediol, and
1,4-cyclohexanedimethanol were prepared as described below, having
the composition and properties shown on Table 5. The balance up to
100 mol % of the diol component of the polyesters in Table 5 was
1,4-cyclohexanedimethanol (31/69 cis/trans).
[1158] Materials were injection molded into both 3.2 mm and 6.4 mm
thick bars and subsequently notched for Izod impact testing. The
notched Izod impact strengths were obtained at 23.degree. C. and
are reported in Table 5. Density, Tg, and crystallization halftime
were measured on the molded bars. Melt viscosity was measured on
pellets at 290.degree. C. TABLE-US-00006 TABLE 5 Compilation of
various properties for certain polyesters useful in the invention
Notched Notched Izod of Izod of 3.2 mm 6.4 mm Melt thick thick
Crystallization Viscosity Pellet Molded bars at bars at Specific
Halftime from at 1 rad/sec TMCD % cis IV Bar IV 23.degree. C.
23.degree. C. Gravity Tg melt at 170.degree. C. at 290.degree. C.
Example mole % TMCD (dl/g) (dl/g) (J/m) (J/m) (g/mL) (.degree. C.)
(min) (Poise) A 44 46.2 0.657 0.626 727 734 1.172 119 NA 9751 B 45
NA 0.626 0.580 748 237 1.167 123 NA 8051 C 45 NA 0.582 0.550 671
262 1.167 125 19782 5835 D 45 NA 0.541 0.493 424 175 1.167 123 NA
3275 E 59 46.6 0.604 0.576 456 311 1.156 139 NA 16537 F 45 47.2
0.475 0.450 128 30 1.169 121 NA 1614 NA = Not available.
Example 5A
[1159] 21.24 lb (49.71 gram-mol) dimethyl terephthalate, 8.84 lb
(27.88 gram-mol) 1,4-cyclohexanedimethanol, and 10.08 lb (31.77
gram-mol) 2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted
together in the presence of 200 ppm of the catalyst butyltin
tris(2-ethylhexanoate). The reaction was carried out under a
nitrogen gas purge in an 18-gallon stainless steel pressure vessel
fitted with a condensing column, a vacuum system, and a
HELICONE-type agitator. With the agitator running at 25 RPM, the
reaction mixture temperature was increased to 250.degree. C. and
the pressure was increased to 20 psig. The reaction mixture was
held for 2 hours at 250.degree. C. and 20 psig pressure. The
pressure was then decreased to 0 psig at a rate of 3 psig/minute.
Then the agitator speed was decreased to 15 RPM, the temperature of
the reaction mixture was then increased to 290.degree. C. and the
pressure was decreased to 2 mm of Hg. The reaction mixture was held
at 290.degree. C. and at a pressure of 2 mm of Hg until the power
draw to the agitator no longer increased (80 minutes). The pressure
of the pressure vessel was then increased to 1 atmosphere using
nitrogen gas. The molten polymer was then extruded from the
pressure vessel. The cooled, extruded polymer was ground to pass a
6-mm screen. The polymer had an inherent viscosity of 0.657 dL/g
and a Tg of 119.degree. C. NMR analysis showed that the polymer was
composed of 56.3 mol % 1,4-cyclohexane-dimethanol residues and 43.7
mol % 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer
had color values of: L*=75.04, a*=-1.82, and b*=6.72.
Example 5B to Example 5D
[1160] The polyesters described in Example 5B to Example 5D were
prepared following a procedure similar to the one described for
Example 5A. The composition and properties of these polyesters are
shown in Table 5.
Example 5E
[1161] 21.24 lb (49.71 gram-mol) dimethyl terephthalate, 6.43 lb
(20.28 gram-mol 1,4-cyclohexanedimethanol, and 12.49 lb (39.37
gram-mol) 2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted
together in the presence of 200 ppm of the catalyst butyltin
tris(2-ethylhexanoate). The reaction was carried out under a
nitrogen gas purge in an 18-gallon stainless steel pressure vessel
fitted with a condensing column, a vacuum system, and a
HELICONE-type agitator. With the agitator running at 25 RPM, the
reaction mixture temperature was increased to 250.degree. C. and
the pressure was increased to 20 psig. The reaction mixture was
held for 2 hours at 250.degree. C. and 20 psig pressure. The
pressure was then decreased to 0 psig at a rate of 3 psig/minute.
Then the agitator speed was decreased to 15 RPM, the temperature of
the reaction mixture was then increased to 290.degree. C. and the
pressure was decreased to 2 mm of Hg. The reaction mixture was held
at 290.degree. C. and at a pressure of <1 mm of Hg until the
power draw to the agitator no longer increased (50 minutes). The
pressure of the pressure vessel was then increased to 1 atmosphere
using nitrogen gas. The molten polymer was then extruded from the
pressure vessel. The cooled, extruded polymer was ground to pass a
6-mm screen. The polymer had an inherent viscosity of 0.604 dL/g
and a Tg of 139.degree. C. NMR analysis showed that the polymer was
composed of 40.8 mol % 1,4-cyclohexanedimethanol residues and 59.2
mol % 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer
had color values of: L*=80.48, a*=-1.30, and b*=6.82.
Example 5F
[1162] 21.24 lb (49.71 gram-mol) dimethyl terephthalate, 8.84 lb
(27.88 gram-mol) 1,4-cyclohexanedimethanol, and 10.08 lb (31.77
gram-mol) 2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted
together in the presence of 200 ppm of the catalyst butyltin
tris(2-ethylhexanoate). The reaction was carried out under a
nitrogen gas purge in an 18-gallon stainless steel pressure vessel
fitted with a condensing column, a vacuum system, and a
HELICONE-type agitator. With the agitator running at 25 RPM, the
reaction mixture temperature was increased to 250.degree. C. and
the pressure was increased to 20 psig. The reaction mixture was
held for 2 hours at 250.degree. C. and 20 psig pressure. The
pressure was then decreased to 0 psig at a rate of 3 psig/minute.
The temperature of the reaction mixture was then increased to
270.degree. C. and the pressure was decreased to 90 mm of Hg. After
a 1 hour hold time at 270.degree. C. and 90 mm of Hg, the agitator
speed was decreased to 15 RPM and the pressure was decreased to 4
mm of Hg. When the reaction mixture temperature was 270.degree. C.
and the pressure was 4 mm of Hg, the pressure of the pressure
vessel was immediately increased to 1 atmosphere using nitrogen
gas. The molten polymer was then extruded from the pressure vessel.
The cooled, extruded polymer was ground to pass a 6-mm screen. The
polymer had an inherent viscosity of 0.475 dL/g and a Tg of
121.degree. C. NMR analysis showed that the polymer was composed of
55.5 mol % 1,4-cyclohexane-dimethanol residues and 44.5 mol %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer had
color values of: L*=85.63, a*=-0.88, and b*=4.34.
Example 6--Comparative Example
[1163] This example shows data for comparative materials are shown
in Table 6. The PC was Makrolon 2608 from Bayer, with a nominal
composition of 100 mole % bisphenol A residues and 100 mole %
diphenyl carbonate residues. Makrolon 2608 has a nominal melt flow
rate of 20 grams/10 minutes measured at 300 C using a 1.2 kg
weight. The PET was Eastar 9921 from Eastman Chemical Company, with
a nominal composition of 100 mole % terephthalic acid, 3.5 mole %
cyclohexanedimethanol (CHDM) and 96.5 mole % ethylene glycol. The
PETG was Eastar 6763 from Eastman Chemical Company, with a nominal
composition of 100 mole % terephthalic acid, 31 mole %
cyclohexanedimethanol (CHDM) and 69 mole % ethylene glycol. The
PCTG was Eastar DN001 from Eastman Chemical Company, with a nominal
composition of 100 mole % terephthalic acid, 62 mole %
cyclohexanedimethanol (CHDM) and 38 mole % ethylene glycol. The
PCTA was Eastar AN001 from Eastman Chemical Company, with a nominal
composition of 65 mole % terephthalic acid, 35 mole % isophthalic
acid and 100 mole % cyclohexanedimethanol (CHDM). The Polysulfone
was Udel 1700 from Solvay, with a nominal composition of 100 mole %
bisphenol A residues and 100 mole % 4,4-dichlorosulfonyl sulfone
residues. Udel 1700 has a nominal melt flow rate of 6.5 grams/10
minutes measured at 343 C using a 2.16 kg weight. The SAN was
Lustran 31 from Lanxess, with a nominal composition of 76 weight %
styrene and 24 weight % acrylonitrile. Lustran 31 has a nominal
melt flow rate of 7.5 grams/10 minutes measured at 230 C using a
3.8 kg weight. The examples of the invention show improved
toughness in 6.4 mm thickness bars compared to all of the other
resins. TABLE-US-00007 TABLE 6 Compilation of various properties
for certain commercial polymers Notched Notched Izod of Izod of 3.2
mm 6.4 mm thick thick Crystallization Pellet Molded bars at bars at
Specific Halftime from Polymer IV Bar IV 23.degree. C. 23.degree.
C. Gravity Tg melt Example name (dl/g) (dl/g) (J/m) (J/m) (g/mL)
(.degree. C.) (min) A PC 12 MFR NA 929 108 1.20 146 NA B PCTG 0.73
0.696 NB 70 1.23 87 30 at 170.degree. C. C PCTA 0.72 0.702 98 59
1.20 87 15 at 150.degree. C. D PETG 0.75 0.692 83 59 1.27 80 2500
at 130.degree. C. E PET 0.76 0.726 45 48 1.33 78 1.5 at 170.degree.
C. F SAN 7.5 MFR NA 21 NA 1.07 .about.110 NA G PSU 6.5 MFR NA 69 NA
1.24 .about.190 NA NA = Not available
Example 7
[1164] This example illustrates the effect of the amount of
2,2,4,4-tetramethyl-1,3-cyclobutanediol used for the preparation of
the polyesters of the invention on the glass transition temperature
of the polyesters. Polyesters prepared in this example comprise
from 15 to 25 mol % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol
residues.
Example 7A to Example 7G
[1165] Dimethyl terephthalate, 1,4-cyclohexanedimethanol, and
2,2,4,4-tetramethyl-1,3-cyclobutanediol were weighed into a 500-ml
single neck round bottom flask. NMR analysis on the
2,2,4,4-tetramethyl-1,3-cyclobutanediol starting material showed a
cis/trans ratio of 53/47. The polyesters of this example were
prepared with a 1.2/1 glycol/acid ratio with the entire excess
coming from the 2,2,4,4-tetramethyl-1,3-cyclobutanediol. Enough
dibutyltin oxide catalyst was added to give 300 ppm tin in the
final polymer. The flask was under a 0.2 SCFC nitrogen purge with
vacuum reduction capability. The flask was immersed in a Belmont
metal bath at 200.degree. C. and stirred at 200 RPM after the
reactants had melted. After about 2.5 hours, the temperature was
raised to 210.degree. C. and these conditions were held for an
additional 2 hours. The temperature was raised to 285.degree. C.
(in approximately 25 minutes) and the pressure was reduced to 0.3
mm of Hg over a period of 5 minutes. The stirring was reduced as
the viscosity increased, with 15 RPM being the minimum stirring
used. The total polymerization time was varied to attain the target
inherent viscosities. After the polymerization was complete, the
Belmont metal bath was lowered and the polymer was allowed to cool
to below its glass transition temperature. After about 30 minutes,
the flask was reimmersed in the Belmont metal bath (the temperature
had been increased to 295.degree. C. during this 30 minute wait)
and the polymer mass was heated until it pulled away from the glass
flask. The polymer mass was stirred at mid level in the flask until
the polymer had cooled. The polymer was removed from the flask and
ground to pass a 3 mm screen. Variations to this procedure were
made to produce the copolyesters described below with a targeted
composition of 20 mol %.
[1166] Inherent viscosities were measured as described in the
"Measurement Methods" section above. The compositions of the
polyesters were determined by .sup.1H NMR as explained before in
the Measurement Methods section. The glass transition temperatures
were determined by DSC, using the second heat after quench at a
rate of 20.degree. C./min.
Example 7H to Example 7Q
[1167] These polyesters were prepared by carrying out the ester
exchange and polycondensation reactions in separate stages. The
ester exchange experiments were conducted in a continuous
temperature rise (CTR) reactor. The CTR was a 3000 ml glass reactor
equipped with a single shaft impeller blade agitator, covered with
an electric heating mantle and fitted with a heated packed reflux
condenser column. The reactor was charged with 777 g (4 moles) of
dimethyl terephthalate, 230 g (1.6 moles) of
2,2,4,4-tetramethyl-1,3-cyclobutanediol, 460.8 g (3.2 moles) of
cyclohexanedimethanol and 1.12 g of butyltin tris-2-ethylhexanoate
(such that there will be 200 ppm tin metal in the final polymer).
The heating mantle was set manually to 100% output. The set points
and data collection were facilitated by a Camile process control
system. Once the reactants were melted, stirring was initiated and
slowly increased to 250 rpm. The temperature of the reactor
gradually increased with run time. The weight of methanol collected
was recorded via balance. The reaction was stopped when methanol
evolution stopped or at a pre-selected lower temperature of
260.degree. C. The oligomer was discharged with a nitrogen purge
and cooled to room temperature. The oligomer was frozen with liquid
nitrogen and broken into pieces small enough to be weighed into a
500 ml round bottom flask.
[1168] In the polycondensation reactions, a 500 ml round bottom
flask was charged with approximately 150 g of the oligomer prepared
above. The flask was equipped with a stainless steel stirrer and
polymer head. The glassware was set up on a half mole polymer rig
and the Camile sequence was initiated. The stirrer was positioned
one full turn from the flask bottom once the oligomer melted. The
temperature/pressure/stir rate sequence controlled by the Camile
software for each example is reported in the following tables.
[1169] Camile Sequence for Example 7 H and Example 7I
TABLE-US-00008 Time Vacuum Stir Stage (min) Temp (.degree. C.)
(torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 760 50 4 3 265
90 50 5 110 290 90 50 6 5 290 6 25 7 110 290 6 25
[1170] Camile Sequence for Example 7N to Example 7Q TABLE-US-00009
Time Vacuum Stir Stage (min) Temp (.degree. C.) (torr) (rpm) 1 5
245 760 0 2 5 245 760 50 3 30 265 760 50 4 3 265 90 50 5 110 290 90
50 6 5 290 3 25 7 110 290 3 25
[1171] Camile Sequence for Example 7K and Example 7L TABLE-US-00010
Time Vacuum Stir Stage (min) Temp (.degree. C.) (torr) (rpm) 1 5
245 760 0 2 5 245 760 50 3 30 265 760 50 4 3 265 90 50 5 110 290 90
50 6 5 290 2 25 7 110 290 2 25
[1172] Camile Sequence for Example 7J and Example 7M TABLE-US-00011
Time Vacuum Stir Stage (min) Temp (.degree. C.) (torr) (rpm) 1 5
245 760 0 2 5 245 760 50 3 30 265 760 50 4 3 265 90 50 5 110 290 90
50 6 5 290 1 25 7 110 290 1 25
[1173] The resulting polymers were recovered from the flask,
chopped using a hydraulic chopper, and ground to a 6 mm screen
size. Samples of each ground polymer were submitted for inherent
viscosity in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C., catalyst level (Sn)
by x-ray fluorescence, and color (L*, a*, b*) by transmission
spectroscopy. Polymer composition was obtained by .sup.1H NMR.
Samples were submitted for thermal stability and melt viscosity
testing using a Rheometrics Mechanical Spectrometer (RMS-800).
[1174] The table below shows the experimental data for the
polyesters of this example. The data shows that an increase in the
level of 2,2,4,4-tetramethyl-1,3-cyclobutanediol raises the glass
transition temperature in an almost linear fashion, for a constant
inherent viscosity. FIG. 3 also shows the dependence of Tg on
composition and inherent viscosity. TABLE-US-00012 TABLE 7 Glass
transition temperature as a function of inherent viscosity and
composition % cis .eta..sub.o at 260.degree. C. .eta..sub.o at
275.degree. C. .eta..sub.o at 290.degree. C. Example mol % TMCD
TMCD IV (dL/g) T.sub.g (.degree. C.) (Poise) (Poise) (Poise) A 20
51.4 0.72 109 11356 19503 5527 B 19.1 51.4 0.60 106 6891 3937 2051
C 19 53.2 0.64 107 8072 4745 2686 D 18.8 54.4 0.70 108 14937 8774
4610 E 17.8 52.4 0.50 103 3563 1225 883 F 17.5 51.9 0.75 107 21160
10877 5256 G 17.5 52 0.42 98 NA NA NA H 22.8 53.5 0.69 109 NA NA NA
I 22.7 52.2 0.68 108 NA NA NA J 23.4 52.4 0.73 111 NA NA NA K 23.3
52.9 0.71 111 NA NA NA L 23.3 52.4 0.74 112 NA NA NA M 23.2 52.5
0.74 112 NA NA NA N 23.1 52.5 0.71 111 NA NA NA O 22.8 52.4 0.73
112 NA NA NA P 22.7 53 0.69 112 NA NA NA Q 22.7 52 0.70 111 NA NA
NA NA = Not available
Example 8
[1175] This example illustrates the effect of the amount of
2,2,4,4-tetramethyl-1,3-cyclobutanediol used for the preparation of
the polyesters of the invention on the glass transition temperature
of the polyesters. Polyesters prepared in this example fall
comprise more than 25 to less than 40 mol % of
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.
[1176] Dimethyl terephthalate, 1,4-cyclohexanedimethanol, and
2,2,4,4-tetramethyl-1,3-cyclobutanediol were weighed into a 500-ml
single neck round bottom flask. NMR analysis on the
2,2,4,4-tetramethyl-1,3-cyclobutanediol starting material showed a
cis/trans ratio of 53/47. The polyesters of this example were
prepared with a 1.2/1 glycol/acid ratio with the entire excess
coming from the 2,2,4,4-tetramethyl-1,3-cyclobutanediol. Enough
dibutyltin oxide catalyst was added to give 300 ppm tin in the
final polymer. The flask was under a 0.2 SCFC nitrogen purge with
vacuum reduction capability. The flask was immersed in a Belmont
metal bath at 200.degree. C. and stirred at 200 RPM after the
reactants had melted. After about 2.5 hours, the temperature was
raised to 210.degree. C. and these conditions were held for an
additional 2 hours. The temperature was raised to 285.degree. C.
(in approximately 25 minutes) and the pressure was reduced to 0.3
mm of Hg over a period of 5 minutes. The stirring was reduced as
the viscosity increased, with 15 RPM being the minimum stirring
used. The total polymerization time was varied to attain the target
inherent viscosities. After the polymerization was complete, the
Belmont metal bath was lowered and the polymer was allowed to cool
to below its glass transition temperature. After about 30 minutes,
the flask was reimmersed in the Belmont metal bath (the temperature
had been increased to 295.degree. C. during this 30 minute wait)
and the polymer mass was heated until it pulled away from the glass
flask. The polymer mass was stirred at mid level in the flask until
the polymer had cooled. The polymer was removed from the flask and
ground to pass a 3 mm screen. Variations to this procedure were
made to produce the copolyesters described below with a targeted
composition of 32 mol %.
[1177] Inherent viscosities were measured as described in the
"Measurement Methods" section above. The compositions of the
polyesters were determined by .sup.1H NMR as explained before in
the Measurement Methods section. The glass transition temperatures
were determined by DSC, using the second heat after quench at a
rate of 20.degree. C./min.
[1178] The table below shows the experimental data for the
polyesters of this example. FIG. 3 also shows the dependence of Tg
on composition and inherent viscosity. The data shows that an
increase in the level of 2,2,4,4-tetramethyl-1,3-cyclobutanediol
raises the glass transition temperature in an almost linear
fashion, for a constant inherent viscosity. TABLE-US-00013 TABLE 8
Glass transition temperature as a function of inherent viscosity
and composition .eta..sub.o at % cis .eta..sub.o at 260.degree. C.
275.degree. C. .eta..sub.o at 290.degree. C. Example mol % TMCD
TMCD IV (dL/g) T.sub.g (.degree. C.) (Poise) (Poise) (Poise) A 32.2
51.9 0.71 118 29685 16074 8522 B 31.6 51.5 0.55 112 5195 2899 2088
C 31.5 50.8 0.62 112 8192 4133 2258 D 30.7 50.7 0.54 111 4345 2434
1154 E 30.3 51.2 0.61 111 7929 4383 2261 F 30.0 51.4 0.74 117 31476
17864 8630 G 29.0 51.5 0.67 112 16322 8787 4355 H 31.1 51.4 0.35
102 NA NA NA NA = Not available
Example 9
[1179] This example illustrates the effect of the amount of
2,2,4,4-tetramethyl-1,3-cyclobutanediol used for the preparation of
the polyesters of the invention on the glass transition temperature
of the polyesters. Polyesters prepared in this example comprise
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues in an amount of 40
mol % or greater.
Examples A to AC
[1180] These polyesters were prepared by carrying out the ester
exchange and polycondensation reactions in separate stages. The
ester exchange experiments were conducted in a continuous
temperature rise (CTR) reactor. The CTR was a 3000 ml glass reactor
equipped with a single shaft impeller blade agitator, covered with
an electric heating mantle and fitted with a heated packed reflux
condenser column. The reactor was charged with 777 g of dimethyl
terephthalate, 375 g of 2,2,4,4-tetramethyl-1,3-cyclobutanediol,
317 g of cyclohexanedimethanol and 1.12 g of butyltin
tris-2-ethylhexanoate (such that there will be 200 ppm tin metal in
the final polymer). The heating mantle was set manually to 100%
output. The set points and data collection were facilitated by a
Camile process control system. Once the reactants were melted,
stirring was initiated and slowly increased to 250 rpm. The
temperature of the reactor gradually increased with run time. The
weight of methanol collected was recorded via balance. The reaction
was stopped when methanol evolution stopped or at a pre-selected
lower temperature of 260.degree. C. The oligomer was discharged
with a nitrogen purge and cooled to room temperature. The oligomer
was frozen with liquid nitrogen and broken into pieces small enough
to be weighed into a 500 ml round bottom flask.
[1181] In the polycondensation reactions, a 500 ml round bottom
flask was charged with 150 g of the oligomer prepared above. The
flask was equipped with a stainless steel stirrer and polymer head.
The glassware was set up on a half mole polymer rig and the Camile
sequence was initiated. The stirrer was positioned one full turn
from the flask bottom once the oligomer melted. The
temperature/pressure/stir rate sequence controlled by the Camile
software for these examples is reported in the following table,
unless otherwise specified below. TABLE-US-00014 Camile Sequence
for Polycondensation Reactions Time Vacuum Stir Stage (min) Temp
(.degree. C.) (torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265
760 50 4 3 265 90 50 5 110 290 90 50 6 5 290 6 25 7 110 290 6
25
[1182] Camile Sequence for Examples A, C, R, Y, AB, AC
TABLE-US-00015 Time Vacuum Stir Stage (min) Temp (.degree. C.)
(torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 760 50 4 3 265
90 50 5 110 290 90 50 6 5 290 6 25 7 110 290 6 25
[1183] For Examples B, D, F, the same sequence in the preceding
table was used, except the time was 80 min in Stage 7. For Examples
G and J, the same sequence in the preceding table was used, except
the time was 50 min in Stage 7. For Example L, the same sequence in
the preceding table was used, except the time was 140 min in Stage
7.
[1184] Camile Sequence for Example E TABLE-US-00016 Time Vacuum
Stir Stage (min) Temp (.degree. C.) (torr) (rpm) 1 5 245 760 0 2 5
245 760 50 3 30 265 760 50 4 3 265 90 50 5 110 300 90 50 6 5 300 7
25 7 110 300 7 25
[1185] For Example I, the same sequence in the preceding table was
used, except the vacuum was 8 torr in Stages 6 and 7. For Example
O, the same sequence in the preceding table was used, except the
vacuum was 6 torr in Stages 6 and 7. For Example P, the same
sequence in the preceding table was used, except the vacuum was 4
torr in Stages 6 and 7. For Example Q, the same sequence in the
preceding table was used, except the vacuum was 5 torr in Stages 6
and 7.
[1186] Camile Sequence for Example H TABLE-US-00017 Time Vacuum
Stir Stage (min) Temp (.degree. C.) (torr) (rpm) 1 5 245 760 0 2 5
245 760 50 3 30 265 760 50 4 3 265 90 50 5 110 280 90 50 6 5 280 5
25 7 110 280 5 25
[1187] For Example U and AA, the same sequence in the preceding
table was used, except the vacuum was 6 torr in Stages 6 and 7. For
Example V and X, the same sequence in the preceding table was used,
except the vacuum was 6 torr and stir rate was 15 rpm in Stages 6
and 7. For Example Z, the same sequence in the preceding table was
used, except the stir rate was 15 rpm in Stages 6 and 7.
[1188] Camile Sequence for Example K TABLE-US-00018 Time Vacuum
Stir Stage (min) Temp (.degree. C.) (torr) (rpm) 1 5 245 760 0 2 5
245 760 50 3 30 265 760 50 4 3 265 90 50 5 110 300 90 50 6 5 300 6
15 7 110 300 6 15
[1189] For Example M, the same sequence in the preceding table was
used, except the vacuum was 8 torr in Stages 6 and 7. For Example
N, the same sequence in the preceding table was used, except the
vacuum was 7 torr in Stages 6 and 7.
[1190] Camile Sequence for Examples S and T TABLE-US-00019 Time
Temp Vacuum Stir Stage (min) (.degree. C.) (torr) (rpm) 1 5 245 760
0 2 5 245 760 50 3 30 265 760 50 4 5 290 6 25 5 110 290 6 25
[1191] The resulting polymers were recovered from the flask,
chopped using a hydraulic chopper, and ground to a 6 mm screen
size. Samples of each ground polymer were submitted for inherent
viscosity in 60/40 (wt/wt) phenol/tetrachloroethane at a
concentration of 0.5 g/100 ml at 25.degree. C., catalyst level (Sn)
by x-ray fluorescence, and color (L*, a*, b*) by transmission
spectroscopy. Polymer composition was obtained by 1H NMR. Samples
were submitted for thermal stability and melt viscosity testing
using a Rheometrics Mechanical Spectrometer (RMS-800).
Examples AD to AK and AT
[1192] The polyesters of these examples were prepared as described
above for Examples A to AC, except that the target tin amount in
the final polymer was 150 ppm for examples AD to AK and AT. The
following tables describe the temperature/pressure/stir rate
sequences controlled by the Camile software for these examples.
[1193] Camile Sequence for Examples AD, AF, and AH TABLE-US-00020
Time Temp Vacuum Stir Stage (min) (.degree. C.) (torr) (rpm) 1 5
245 760 0 2 5 245 760 50 3 30 265 760 50 4 3 265 400 50 5 110 290
400 50 6 5 290 8 50 7 110 295 8 50
[1194] For Example AD, the stirrer was turned to 25 rpm with 95 min
left in Stage 7.
[1195] Camile Sequence for Example AE TABLE-US-00021 Time Temp
Vacuum Stir Stage (min) (.degree. C.) (torr) (rpm) 1 10 245 760 0 2
5 245 760 50 3 30 283 760 50 4 3 283 175 50 5 5 283 5 50 6 5 283
1.2 50 7 71 285 1.2 50
[1196] For Example AK, the same sequence in the preceding table was
used, excepts the time was 75 min in Stage 7.
[1197] Camile Sequence for Example AG TABLE-US-00022 Time Temp
Vacuum Stir Stage (min) (.degree. C.) (torr) (rpm) 1 10 245 760 0 2
5 245 760 50 3 30 285 760 50 4 3 285 175 50 5 5 285 5 50 6 5 285 4
50 7 220 290 4 50
[1198] Camile Sequence for Example AI TABLE-US-00023 Time Temp
Vacuum Stir Stage (min) (.degree. C.) (torr) (rpm) 1 5 245 760 0 2
5 245 760 50 3 30 265 760 50 4 3 265 90 50 5 110 285 90 50 6 5 285
6 50 7 70 290 6 50
[1199] Camile Sequence for Example AJ TABLE-US-00024 Time Temp
Vacuum Stir Stage (min) (.degree. C.) (torr) (rpm) 1 5 245 760 0 2
5 245 760 50 3 30 265 760 50 4 3 265 90 50 5 110 290 90 50 6 5 290
6 25 7 110 295 6 25
Example AL to AS
[1200] Dimethyl terephthalate, 1,4-cyclohexanedimethanol, and
2,2,4,4-tetramethyl-1,3-cyclobutanediol were weighed into a 500-ml
single neck round bottom flask. The polyesters of this example were
prepared with a 1.2/1 glycol/acid ratio with the entire excess
coming from the 2,2,4,4-tetramethyl-1,3-cyclobutanediol. Enough
dibutyltin oxide catalyst was added to give 300 ppm tin in the
final polymer. The flask was under a 0.2 SCFC nitrogen purge with
vacuum reduction capability. The flask was immersed in a Belmont
metal bath at 200.degree. C. and stirred at 200 RPM after the
reactants had melted. After about 2.5 hours, the temperature was
raised to 210.degree. C. and these conditions were held for an
additional 2 hours. The temperature was raised to 285.degree. C.
(in approximately 25 minutes) and the pressure was reduced to 0.3
mm of Hg over a period of 5 minutes. The stirring was reduced as
the viscosity increased, with 15 RPM being the minimum stirring
used. The total polymerization time was varied to attain the target
inherent viscosities. After the polymerization was complete, the
Belmont metal bath was lowered and the polymer was allowed to cool
to below its glass transition temperature. After about 30 minutes,
the flask was reimmersed in the Belmont metal bath (the temperature
had been increased to 295.degree. C. during this 30 minute wait)
and the polymer mass was heated until it pulled away from the glass
flask. The polymer mass was stirred at mid level in the flask until
the polymer had cooled. The polymer was removed from the flask and
ground to pass a 3 mm screen. Variations to this procedure were
made to produce the copolyesters described below with a targeted
composition of 45 mol %.
[1201] Inherent viscosities were measured as described in the
"Measurement Methods" section above. The compositions of the
polyesters were determined by .sup.1H NMR as explained before in
the Measurement Methods section. The glass transition temperatures
were determined by DSC, using the second heat after quench at a
rate of 20.degree. C./min.
[1202] The table below shows the experimental data for the
polyesters of this example. The data shows that an increase in the
level of 2,2,4,4-tetramethyl-1,3-cyclobutanediol raises the glass
transition temperature in an almost linear fashion, for a constant
inherent viscosity. FIG. 3 also shows the dependence of Tg on
composition and inherent viscosity. TABLE-US-00025 TABLE 9 Glass
transition temperature as a function of inherent viscosity and
composition .eta..sub.o at .eta..sub.o at .eta..sub.o at Ex- mol %
% cis IV T.sub.g 260.degree. C. 275.degree. C. 290.degree. C. ample
TMCD TMCD (dL/g) (.degree. C.) (Poise) (Poise) (Poise) A 43.9 72.1
0.46 131 NA NA NA B 44.2 36.4 0.49 118 NA NA NA C 44 71.7 0.49 128
NA NA NA D 44.3 36.3 0.51 119 NA NA NA E 46.1 46.8 0.51 125 NA NA
NA F 43.6 72.1 0.52 128 NA NA NA G 43.6 72.3 0.54 127 NA NA NA H
46.4 46.4 0.54 127 NA NA NA I 45.7 47.1 0.55 125 NA NA NA J 44.4
35.6 0.55 118 NA NA NA K 45.2 46.8 0.56 124 NA NA NA L 43.8 72.2
0.56 129 NA NA NA M 45.8 46.4 0.56 124 NA NA NA N 45.1 47.0 0.57
125 NA NA NA O 45.2 46.8 0.57 124 NA NA NA P 45 46.7 0.57 125 NA NA
NA Q 45.1 47.1 0.58 127 NA NA NA R 44.7 35.4 0.59 123 NA NA NA S
46.1 46.4 0.60 127 NA NA NA T 45.7 46.8 0.60 129 NA NA NA U 46 46.3
0.62 128 NA NA NA V 45.9 46.3 0.62 128 NA NA NA X 45.8 46.1 0.63
128 NA NA NA Y 45.6 50.7 0.63 128 NA NA NA Z 46.2 46.8 0.65 129 NA
NA NA AA 45.9 46.2 0.66 128 NA NA NA AB 45.2 46.4 0.66 128 NA NA NA
AC 45.1 46.5 0.68 129 NA NA NA AD 46.3 52.4 0.52 NA NA NA NA AE
45.7 50.9 0.54 NA NA NA NA AF 46.3 52.6 0.56 NA NA NA NA AG 46 50.6
0.56 NA NA NA NA AH 46.5 51.8 0.57 NA NA NA NA AI 45.6 51.2 0.58 NA
NA NA NA AJ 46 51.9 0.58 NA NA NA NA AK 45.5 51.2 0.59 NA NA NA NA
AL 45.8 50.1 0.624 125 NA NA 7696 AM 45.7 49.4 0.619 128 NA NA 7209
AN 46.2 49.3 0.548 124 NA NA 2348 AP 45.9 49.5 0.72 128 76600 40260
19110 AQ 46.0 50 0.71 131 68310 32480 17817 AR 46.1 49.6 0.383 117
NA NA 387 AS 45.6 50.5 0.325 108 NA NA NA AT 47.2 NA 0.48 NA NA NA
NA NA = Not available
Example 10
[1203] This example illustrates the effect of the predominance of
the type of 2,2,4,4-tetramethyl-1,3-cyclobutanediol isomer (cis or
trans) on the glass transition temperature of the polyester.
[1204] Dimethyl terephthalate, 1,4-cyclohexanedimethanol, and
2,2,4,4-tetramethyl-1,3-cyclobutanediol were weighed into a 500-ml
single neck round bottom flask. The polyesters of this example were
prepared with a 1.2/1 glycol/acid ratio with the entire excess
coming from the 2,2,4,4-tetramethyl-1,3-cyclobutanediol. Enough
dibutyltin oxide catalyst was added to give 300 ppm tin in the
final polymer. The flask was under a 0.2 SCFC nitrogen purge with
vacuum reduction capability. The flask was immersed in a Belmont
metal bath at 200.degree. C. and stirred at 200 RPM after the
reactants had melted. After about 2.5 hours, the temperature was
raised to 210.degree. C. and these conditions were held for an
additional 2 hours. The temperature was raised to 285.degree. C.
(in approximately 25 minutes) and the pressure was reduced to 0.3
mm of Hg over a period of 5 minutes. The stirring was reduced as
the viscosity increased, with 15 RPM being the minimum stirring
used. The total polymerization time was varied to attain the target
inherent viscosities. After the polymerization was complete, the
Belmont metal bath was lowered and the polymer was allowed to cool
to below its glass transition temperature. After about 30 minutes,
the flask was reimmersed in the Belmont metal bath (the temperature
had been increased to 295.degree. C. during this 30 minute wait)
and the polymer mass was heated until it pulled away from the glass
flask. The polymer mass was stirred at mid level in the flask until
the polymer had cooled. The polymer was removed from the flask and
ground to pass a 3 mm screen. Variations to this procedure were
made to produce the copolyesters described below with a targeted
composition of 45 mol %.
[1205] Inherent viscosities were measured as described in the
"Measurement Methods" section above. The compositions of the
polyesters were determined by .sup.1H NMR as explained before in
the Measurement Methods section. The glass transition temperatures
were determined by DSC, using the second heat after quench at a
rate of 20.degree. C./min.
[1206] The table below shows the experimental data for the
polyesters of this Example. The data shows that cis
2,2,4,4-tetramethyl-1,3-cyclobutanediol is approximately twice as
effective as trans 2,2,4,4-tetramethyl-1,3-cyclobutanediol at
increasing the glass transition temperature for a constant inherent
viscosity. TABLE-US-00026 TABLE 10 Effect of
2,2,4,4-tetramethyl-1,3-cyclobutanediol cis/trans composition on
T.sub.g .eta..sub.o at .eta..sub.o at .eta..sub.o at Ex- mol % IV
T.sub.g 260.degree. C. 275.degree. C. 290.degree. C. % cis ample
TMCD (dL/g) (.degree. C.) (Poise) (Poise) (Poise) TMCD A 45.8 0.71
119 N.A. N.A. N.A. 4.1 B 43.2 0.72 122 N.A. N.A. N.A. 22.0 C 46.8
0.57 119 26306 16941 6601 22.8 D 43.0 0.67 125 55060 36747 14410
23.8 E 43.8 0.72 127 101000 62750 25330 24.5 F 45.9 0.533 119 11474
6864 2806 26.4 G 45.0 0.35 107 N.A. N.A. N.A. 27.2 H 41.2 0.38 106
1214 757 N.A. 29.0 I 44.7 0.59 123 N.A. N.A. N.A. 35.4 J 44.4 0.55
118 N.A. N.A. N.A. 35.6 K 44.3 0.51 119 N.A. N.A. N.A. 36.3 L 44.0
0.49 128 N.A. N.A. N.A. 71.7 M 43.6 0.52 128 N.A. N.A. N.A. 72.1 N
43.6 0.54 127 N.A. N.A. N.A. 72.3 O 41.5 0.58 133 15419 10253 4252
88.7 P 43.8 0.57 135 16219 10226 4235 89.6 Q 41.0 0.33 120 521 351
2261 90.4 R 43.0 0.56 134 N.A. NA. N.A. 90.6 S 43.0 0.49 132 7055
4620 2120 90.6 T 43.1 0.55 134 12970 8443 3531 91.2 U 45.9 0.52 137
N.A. N.A. N.A. 98.1 NA = not available
Example 11
[1207] This example illustrates the preparation of a copolyester
containing 100 mol % dimethyl terephthalate residues, 55 mol %
1,4-cyclohexanedimethanol residues, and 45 mol %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.
[1208] A mixture of 97.10 g (0.5 mol) dimethyl terephthalate, 52.46
g (0.36 mol) 1,4-cyclohexanedimethanol, 34.07 g (0.24 mol)
2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 0.0863 g (300 ppm)
dibutyl tin oxide was placed in a 500-milliliter flask equipped
with an inlet for nitrogen, a metal stirrer, and a short
distillation column. The flask was placed in a Wood's metal bath
already heated to 200.degree. C. The contents of the flask were
heated at 200.degree. C. for 1 hour and then the temperature was
increased to 210.degree. C. The reaction mixture was held at
210.degree. C. for 2 hours and then heated up to 290.degree. C. in
30 minutes. Once at 290.degree. C., a vacuum of 0.01 psig was
gradually applied over the next 3 to 5 minutes. Full vacuum (0.01
psig) was maintained for a total time of about 45 minutes to remove
excess unreacted diols. A high melt viscosity, visually clear and
colorless polymer was obtained with a glass transition temperature
of 125.degree. C. and an inherent viscosity of 0.64 dL/g.
Example 12--Comparative Example
[1209] This example illustrates that a polyester based on 100%
2,2,4,4-tetramethyl-1,3-cyclobutanediol has a slow crystallization
half-time.
[1210] A polyester based solely on terephthalic acid and
2,2,4,4-tetramethyl-1,3-cyclobutanediol was prepared in a method
similar to the method described in Example 1A with the properties
shown on Table 11. This polyester was made with 300 ppm dibutyl tin
oxide. The trans/cis ratio of the
2,2,4,4-tetramethyl-1,3-cyclobutanediol was 65/35.
[1211] Films were pressed from the ground polymer at 320.degree. C.
Crystallization half-time measurements from the melt were made at
temperatures from 220 to 250.degree. C. at 10.degree. C. increments
and are reported in Table 11. The fastest crystallization half-time
for the sample was taken as the minimum value of crystallization
half-time as a function of temperature. The fastest crystallization
half-time of this polyester is around 1300 minutes. This value
contrasts with the fact that the polyester (PCT) based solely on
terephthalic acid and 1,4-cyclohexanedimethanol (no comonomer
modification) has an extremely short crystallization half-time
(<1 min) as shown in FIG. 1. TABLE-US-00027 TABLE 11
Crystallization Half-times (min) at at at at Comonomer IV T.sub.g
T.sub.max 220.degree. C. 230.degree. C. 240.degree. C. 250.degree.
C. (mol %) (dl/g) (.degree. C.) (.degree. C.) (min) (min) (min)
(min) 100 mol % F 0.63 170.0 330 3291 3066 1303 1888 where: F is
2,2,4,4-Tetramethyl-1,3-cyclobutanediol (65/35 Trans/Cis)
Example 13
[1212] Sheets comprising a polyester that had been prepared with a
target composition of 100 mole % terephthalic acid residues, 80
mole % 1,4-cyclohexanedimethanol residues, and 20 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues were produced
using a 3.5 inch single screw extruder. A sheet was extruded
continuously, gauged to a thickness of 177 mil and then various
sheets were sheared to size. Inherent viscosity and glass
transition temperature were measured on one sheet. The sheet
inherent viscosity was measured to be 0.69 dL/g. The glass
transition temperature of the sheet was measured to be 106.degree.
C. Sheets were then conditioned at 50% relative humidity and
60.degree. C. for 2 weeks. Sheets were subsequently thermoformed
into a female mold having a draw ratio of 2.5:1 using a Brown
thermoforming machine. The thermoforming oven heaters were set to
70/60/60% output using top heat only. Sheets were left in the oven
for various amounts of time in order to determine the effect of
sheet temperature on the part quality as shown in the table below.
Part quality was determined by measuring the volume of the
thermoformed part, calculating the draw, and visually inspecting
the thermoformed part. The draw was calculated as the part volume
divided by the maximum part volume achieved in this set of
experiments (Example G). The thermoformed part was visually
inspected for any blisters and the degree of blistering rated as
none (N), low (L), or high (H). The results below demonstrate that
these thermoplastic sheets with a glass transition temperature of
106.degree. C. can be thermoformed under the conditions shown
below, as evidenced by these sheets having at least 95% draw and no
blistering, without predrying the sheets prior to thermoforming.
TABLE-US-00028 Thermoforming Conditions Part Quality Sheet Part
Heat Time Temperature Volume Blisters Example (s) (.degree. C.)
(mL) Draw (%) (N, L, H) A 86 145 501 64 N B 100 150 500 63 N C 118
156 672 85 N D 135 163 736 94 N E 143 166 760 97 N F 150 168 740 94
L G 159 172 787 100 L
Example 14
[1213] Sheets comprising a polyester that had been prepared with a
target composition of 100 mole % terephthalic acid residues, 80
mole % 1,4-cyclohexanedimethanol residues, and 20 mole %
2,2,4,4-tetramethyl-1,3-cyclobutanediol residues were produced
using a 3.5 inch single screw. A sheet was extruded continuously,
gauged to a thickness of 177 mil and then various sheets were
sheared to size. Inherent viscosity and glass transition
temperature were measured on one sheet. The sheet inherent
viscosity was measured to be 0.69 dL/g. The glass transition
temperature of the sheet was measured to be 106.degree. C. Sheets
were then conditioned at 100% relative humidity and 25.degree. C.
for 2 weeks. Sheets were subsequently thermoformed into a female
mold having a draw ratio of 2.5:1 using a Brown thermoforming
machine. The thermoforming oven heaters were set to 60/40/40%
output using top heat only. Sheets were left in the oven for
various amounts of time in order to determine the effect of sheet
temperature on the part quality as shown in the table below. Part
quality was determined by measuring the volume of the thermoformed
part, calculating the draw, and visually inspecting the
thermoformed part. The draw was calculated as the part volume
divided by the maximum part volume achieved in this set of
experiments (Example G). The thermoformed part was visually
inspected for any blisters and the degree of blistering rated as
none (N), low (L), or high (H). The results below demonstrate that
these thermoplastic sheets with a glass transition temperature of
106.degree. C. can be thermoformed under the conditions shown
below, as evidenced by the production of sheets having at least 95%
draw and no blistering, without predrying the sheets prior to
thermoforming. TABLE-US-00029 Thermoforming Conditions Part Quality
Sheet Part Heat Time Temperature Volume Blisters Example (s)
(.degree. C.) (mL) Draw (%) (N, L, H) A 141 154 394 53 N B 163 157
606 82 N C 185 160 702 95 N D 195 161 698 95 N E 215 163 699 95 L F
230 168 705 96 L G 274 174 737 100 H H 275 181 726 99 H
Example 15--Comparative Example
[1214] Sheets consisting of Kelvx 201 were produced using a 3.5
inch single screw extruder. Kelvx is a blend consisting of 69.85%
PCTG (Eastar from Eastman Chemical Co. having 100 mole %
terephthalic acid residues, 62 mole % 1,4-cyclohexanedimethanol
residues, and 38 mole % ethylene glycol residues); 30% PC
(bisphenol A polycarbonate); and 0.15% Weston 619 (stabilizer sold
by Crompton Corporation). A sheet was extruded continuously, gauged
to a thickness of 177 mil and then various sheets were sheared to
size. The glass transition temperature was measured on one sheet
and was 100.degree. C. Sheets were then conditioned at 50% relative
humidity and 60.degree. C. for 2 weeks. Sheets were subsequently
thermoformed into a female mold having a draw ratio of 2.5:1 using
a Brown thermoforming machine. The thermoforming oven heaters were
set to 70/60/60% output using top heat only. Sheets were left in
the oven for various amounts of time in order to determine the
effect of sheet temperature on the part quality as shown in the
table below. Part quality was determined by measuring the volume of
the thermoformed part, calculating the draw, and visually
inspecting the thermoformed part. The draw was calculated as the
part volume divided by the maximum part volume achieved in this set
of experiments (Example E). The thermoformed part was visually
inspected for any blisters and the degree of blistering rated as
none (N), low (L), or high (H). The results below demonstrate that
these thermoplastic sheets with a glass transition temperature of
100.degree. C. can be thermoformed under the conditions shown
below, as evidenced by the production of sheets having at least 95%
draw and no blistering, without predrying the sheets prior to
thermoforming. TABLE-US-00030 Thermoforming Conditions Part Quality
Sheet Part Heat Time Temperature Volume Blisters Example (s)
(.degree. C.) (mL) Draw (%) (N, L, H) A 90 146 582 75 N B 101 150
644 83 N C 111 154 763 98 N D 126 159 733 95 N E 126 159 775 100 N
F 141 165 757 98 N G 148 168 760 98 L
Example 16--Comparative Example
[1215] Sheets consisting of Kelvx 201 were produced using a 3.5
inch single screw extruder. A sheet was extruded continuously,
gauged to a thickness of 177 mil and then various sheets were
sheared to size. The glass transition temperature was measured on
one sheet and was 100.degree. C. Sheets were then conditioned at
100% relative humidity and 25.degree. C. for 2 weeks. Sheets were
subsequently thermoformed into a female mold having a draw ratio of
2.5:1 using a Brown thermoforming machine. The thermoforming oven
heaters were set to 60/40/40% output using top heat only. Sheets
were left in the oven for various amounts of time in order to
determine the effect of sheet temperature on the part quality as
shown in the table below. Part quality was determined by measuring
the volume of the thermoformed part, calculating the draw, and
visually inspecting the thermoformed part. The draw was calculated
as the part volume divided by the maximum part volume achieved in
this set of experiments (Example H). The thermoformed part was
visually inspected for any blisters and the degree of blistering
rated as none (N), low (L), or high (H). The results below
demonstrate that these thermoplastic sheets with a glass transition
temperature of 100.degree. C. can be thermoformed under the
conditions shown below, as evidenced by the production of sheets
having greater than 95% draw and no blistering, without predrying
the sheets prior to thermoforming. TABLE-US-00031 Thermoforming
Conditions Part Quality Sheet Part Heat Time Temperature Volume
Blisters Example (s) (.degree. C.) (mL) Draw (%) (N, L, H) A 110
143 185 25 N B 145 149 529 70 N C 170 154 721 95 N D 175 156 725 96
N E 185 157 728 96 N F 206 160 743 98 L G 253 NR 742 98 H H 261 166
756 100 H NR = Not recorded
Example 17--Comparative Example
[1216] Sheets consisting of PCTG 25976 (100 mole % terephthalic
acid residues, 62 mole % 1,4-cyclohexanedimethanol residues, and 38
mole % ethylene glycol residues) were produced using a 3.5 inch
single screw extruder. A sheet was extruded continuously, gauged to
a thickness of 118 mil and then various sheets were sheared to
size. The glass transition temperature was measured on one sheet
and was 87.degree. C. Sheets were then conditioned at 50% relative
humidity and 60.degree. C. for 4 weeks. The moisture level was
measured to be 0.17 wt %. Sheets were subsequently thermoformed
into a female mold having a draw ratio of 2.5:1 using a Brown
thermoforming machine. The thermoforming oven heaters were set to
70/60/60% output using top heat only. Sheets were left in the oven
for various amounts of time in order to determine the effect of
sheet temperature on the part quality as shown in the table below.
Part quality was determined by measuring the volume of the
thermoformed part, calculating the draw, and visually inspecting
the thermoformed part. The draw was calculated as the part volume
divided by the maximum part volume achieved in this set of
experiments (Example A). The thermoformed part was visually
inspected for any blisters and the degree of blistering rated as
none (N), low (L), or high (H). The results below demonstrate that
these thermoplastic sheets with a glass transition temperature of
87.degree. C. can be thermoformed under the conditions shown below,
as evidenced by the production of sheets having greater than 95%
draw and no blistering, without predrying the sheets prior to
thermoforming. TABLE-US-00032 Thermoforming Conditions Part Quality
Sheet Part Heat Time Temperature Volume Blisters Example (s)
(.degree. C.) (mL) Draw (%) (N, L, H) A 102 183 816 100 N B 92 171
811 99 N C 77 160 805 99 N D 68 149 804 99 N E 55 143 790 97 N F 57
138 697 85 N
Example 18--Comparative Example
[1217] A miscible blend consisting of 20 wt % Teijin L-1250
polycarbonate (a bisphenol-A polycarbonate), 79.85 wt % PCTG 25976,
and 0.15 wt % Weston 619 was produced using a 1.25 inch single
screw extruder. Sheets consisting of the blend were then produced
using a 3.5 inch single screw extruder. A sheet was extruded
continuously, gauged to a thickness of 118 mil and then various
sheets were sheared to size. The glass transition temperature was
measured on one sheet and was 94.degree. C. Sheets were then
conditioned at 50% relative humidity and 60.degree. C. for 4 weeks.
The moisture level was measured to be 0.25 wt %. Sheets were
subsequently thermoformed into a female mold having a draw ratio of
2.5:1 using a Brown thermoforming machine. The thermoforming oven
heaters were set to 70/60/60% output using top heat only. Sheets
were left in the oven for various amounts of time in order to
determine the effect of sheet temperature on the part quality as
shown in the table below. Part quality was determined by measuring
the volume of the thermoformed part, calculating the draw, and
visually inspecting the thermoformed part. The draw was calculated
as the part volume divided by the maximum part volume achieved in
this set of experiments (Example A). The thermoformed part was
visually inspected for any blisters and the degree of blistering
rated as none (N), low (L), or high (H). The results below
demonstrate that these thermoplastic sheets with a glass transition
temperature of 94.degree. C. can be thermoformed under the
conditions shown below, as evidenced by the production of sheets
having greater than 95% draw and no blistering, without predrying
the sheets prior to thermoforming. TABLE-US-00033 Thermoforming
Conditions Part Quality Sheet Part Heat Time Temperature Volume
Blisters Example (s) (.degree. C.) (mL) Draw (%) (N, L, H) A 92 184
844 100 H B 86 171 838 99 N C 73 160 834 99 N D 58 143 787 93 N E
55 143 665 79 N
Example 19--Comparative Example
[1218] A miscible blend consisting of 30 wt % Teijin L-1250
polycarbonate, 69.85 wt % PCTG 25976, and 0.15 wt % Weston 619 was
produced using a 1.25 inch single screw extruder. Sheets consisting
of the blend were then produced using a 3.5 inch single screw
extruder. A sheet was extruded continuously, gauged to a thickness
of 118 mil and then various sheets were sheared to size. The glass
transition temperature was measured on one sheet and was 99.degree.
C. Sheets were then conditioned at 50% relative humidity and
60.degree. C. for 4 weeks. The moisture level was measured to be
0.25 wt %. Sheets were subsequently thermoformed into a female mold
having a draw ratio of 2.5:1 using a Brown thermoforming machine.
The thermoforming oven heaters were set to 70/60/60% output using
top heat only. Sheets were left in the oven for various amounts of
time in order to determine the effect of sheet temperature on the
part quality as shown in the table below. Part quality was
determined by measuring the volume of the thermoformed part,
calculating the draw, and visually inspecting the thermoformed
part. The draw was calculated as the part volume divided by the
maximum part volume achieved in this set of experiments (Example
A). The thermoformed part was visually inspected for any blisters
and the degree of blistering rated as none (N), low (L), or high
(H). The results below demonstrate that these thermoplastic sheets
with a glass transition temperature of 99.degree. C. can be
thermoformed under the conditions shown below, as evidenced by the
production of sheets having greater than 95% draw and no
blistering, without predrying the sheets prior to thermoforming.
TABLE-US-00034 Thermoforming Conditions Part Quality Sheet Part
Heat Time Temperature Volume Blisters Example (s) (.degree. C.)
(mL) Draw (%) (N, L, H) A 128 194 854 100 H B 98 182 831 97 L C 79
160 821 96 N D 71 149 819 96 N E 55 145 785 92 N F 46 143 0 0 NA G
36 132 0 0 NA NA = not applicable. A value of zero indicates that
the sheet was not formed because it did not pull into the mold
(likely because it was too cold).
Example 20--Comparative Example
[1219] A miscible blend consisting of 40 wt % Teijin L-1250
polycarbonate, 59.85 wt % PCTG 25976, and 0.15 wt % Weston 619 was
produced using a 1.25 inch single screw extruder. Sheets consisting
of the blend were then produced using a 3.5 inch single screw
extruder. A sheet was extruded continuously, gauged to a thickness
of 118 mil and then various sheets were sheared to size. The glass
transition temperature was measured on one sheet and was
105.degree. C. Sheets were then conditioned at 50% relative
humidity and 60.degree. C. for 4 weeks. The moisture level was
measured to be 0.265 wt %. Sheets were subsequently thermoformed
into a female mold having a draw ratio of 2.5:1 using a Brown
thermoforming machine. The thermoforming oven heaters were set to
70/60/60% output using top heat only. Sheets were left in the oven
for various amounts of time in order to determine the effect of
sheet temperature on the part quality as shown in the table below.
Part quality was determined by measuring the volume of the
thermoformed part, calculating the draw, and visually inspecting
the thermoformed part. The draw was calculated as the part volume
divided by the maximum part volume achieved in this set of
experiments (Examples 8A to 8E). The thermoformed part was visually
inspected for any blisters and the degree of blistering rated as
none (N), low (L), or high (H). The results below demonstrate that
these thermoplastic sheets with a glass transition temperature of
105.degree. C. can be thermoformed under the conditions shown
below, as evidenced by the production of sheets having greater than
95% draw and no blistering, without predrying the sheets prior to
thermoforming. TABLE-US-00035 Thermoforming Conditions Part Quality
Sheet Part Heat Time Temperature Volume Blisters Example (s)
(.degree. C.) (mL) Draw (%) (N, L, H) A 111 191 828 100 H B 104 182
828 100 H C 99 179 827 100 N D 97 177 827 100 N E 78 160 826 100 N
F 68 149 759 92 N G 65 143 606 73 N
Example 21--Comparative Example
[1220] A miscible blend consisting of 50 wt % Teijin L-1250
polycarbonate, 49.85 wt % PCTG 25976, and 0.15 wt % Weston 619 was
produced using a 1.25 inch single screw extruder. A sheet was
extruded continuously, gauged to a thickness of 118 mil and then
various sheets were sheared to size. The glass transition
temperature was measured on one sheet and was 111.degree. C. Sheets
were then conditioned at 50% relative humidity and 60.degree. C.
for 4 weeks. The moisture level was measured to be 0.225 wt %.
Sheets were subsequently thermoformed into a female mold having a
draw ratio of 2.5:1 using a Brown thermoforming machine. The
thermoforming oven heaters were set to 70/60/60% output using top
heat only. Sheets were left in the oven for various amounts of time
in order to determine the effect of sheet temperature on the part
quality as shown in the table below. Part quality was determined by
measuring the volume of the thermoformed part, calculating the
draw, and visually inspecting the thermoformed part. The draw was
calculated as the part volume divided by the maximum part volume
achieved in this set of experiments (Examples A to D). The
thermoformed part was visually inspected for any blisters and the
degree of blistering rated as none (N), low (L), or high (H). The
results below demonstrate that these thermoplastic sheets with a
glass transition temperature of 111.degree. C. can be thermoformed
under the conditions shown below, as evidenced by the production of
sheets having greater than 95% draw and no blistering, without
predrying the sheets prior to thermoforming. TABLE-US-00036
Thermoforming Conditions Part Quality Sheet Part Heat Time
Temperature Volume Blisters Example (s) (.degree. C.) (mL) Draw (%)
(N, L, H) A 118 192 815 100 H B 99 182 815 100 H C 97 177 814 100 L
D 87 171 813 100 N E 80 160 802 98 N F 64 154 739 91 N G 60 149 0 0
NA NA = not applicable. A value of zero indicates that the sheet
was not formed because it did not pull into the mold (likely
because it was too cold).
Example 22--Comparative Example
[1221] A miscible blend consisting of 60 wt % Teijin L-1250
polycarbonate, 39.85 wt % PCTG 25976, and 0.15 wt % Weston 619 was
produced using a 1.25 inch single screw extruder. Sheets consisting
of the blend were then produced using a 3.5 inch single screw
extruder. A sheet was extruded continuously, gauged to a thickness
of 118 mil and then various sheets were sheared to size. The glass
transition temperature was measured on one sheet and was
117.degree. C. Sheets were then conditioned at 50% relative
humidity and 60.degree. C. for 4 weeks. The moisture level was
measured to be 0.215 wt %. Sheets were subsequently thermoformed
into a female mold having a draw ratio of 2.5:1 using a Brown
thermoforming machine. The thermoforming oven heaters were set to
70/60/60% output using top heat only. Sheets were left in the oven
for various amounts of time in order to determine the effect of
sheet temperature on the part quality as shown in the table below.
Part quality was determined by measuring the volume of the
thermoformed part, calculating the draw, and visually inspecting
the thermoformed part. The draw was calculated as the part volume
divided by the maximum part volume achieved in this set of
experiments (Example A). The thermoformed part was visually
inspected for any blisters and the degree of blistering rated as
none (N), low (L), or high (H). The results below demonstrate that
these thermoplastic sheets with a glass transition temperature of
117.degree. C. cannot be thermoformed under the conditions shown
below, as evidenced by the inability to produce sheets having
greater than 95% draw and no blistering, without predrying the
sheets prior to thermoforming. TABLE-US-00037 Thermoforming
Conditions Part Quality Sheet Part Heat Time Temperature Volume
Blisters Example (s) (.degree. C.) (mL) Draw (%) (N, L, H) A 114
196 813 100 H B 100 182 804 99 H C 99 177 801 98 L D 92 171 784 96
L E 82 168 727 89 L F 87 166 597 73 N
Example 23--Comparative Example
[1222] A miscible blend consisting of 65 wt % Teijin L-1250
polycarbonate, 34.85 wt % PCTG 25976, and 0.15 wt % Weston 619 was
produced using a 1.25 inch single screw extruder. Sheets consisting
of the blend were then produced using a 3.5 inch single screw
extruder. A sheet was extruded continuously, gauged to a thickness
of 118 mil and then various sheets were sheared to size. The glass
transition temperature was measured on one sheet and was
120.degree. C. Sheets were then conditioned at 50% relative
humidity and 60.degree. C. for 4 weeks. The moisture level was
measured to be 0.23 wt %. Sheets were subsequently thermoformed
into a female mold having a draw ratio of 2.5:1 using a Brown
thermoforming machine. The thermoforming oven heaters were set to
70/60/60% output using top heat only. Sheets were left in the oven
for various amounts of time in order to determine the effect of
sheet temperature on the part quality as shown in the table below.
Part quality was determined by measuring the volume of the
thermoformed part, calculating the draw, and visually inspecting
the thermoformed part. The draw was calculated as the part volume
divided by the maximum part volume achieved in this set of
experiments (Example A). The thermoformed part was visually
inspected for any blisters and the degree of blistering rated as
none (N), low (L), or high (H). The results below demonstrate that
these thermoplastic sheets with a glass transition temperature of
120.degree. C. cannot be thermoformed under the conditions shown
below, as evidenced by the inability to produce sheets having
greater than 95% draw and no blistering, without predrying the
sheets prior to thermoforming. TABLE-US-00038 Thermoforming
Conditions Part Quality Sheet Part Heat Time Temperature Volume
Blisters Example (s) (.degree. C.) (mL) Draw (%) (N, L, H) A 120
197 825 100 H B 101 177 820 99 H C 95 174 781 95 L D 85 171 727 88
L E 83 166 558 68 L
Example 24--Comparative Example
[1223] A miscible blend consisting of 70 wt % Teijin L-1250
polycarbonate, 29.85 wt % PCTG 25976, and 0.15 wt % Weston 619 was
produced using a 1.25 inch single screw extruder. Sheets consisting
of the blend were then produced using a 3.5 inch single screw
extruder. A sheet was extruded continuously, gauged to a thickness
of 118 mil and then various sheets were sheared to size. The glass
transition temperature was measured on one sheet and was
123.degree. C. Sheets were then conditioned at 50% relative
humidity and 60.degree. C. for 4 weeks. The moisture level was
measured to be 0.205 wt %. Sheets were subsequently thermoformed
into a female mold having a draw ratio of 2.5:1 using a Brown
thermoforming machine. The thermoforming oven heaters were set to
70/60/60% output using top heat only. Sheets were left in the oven
for various amounts of time in order to determine the effect of
sheet temperature on the part quality as shown in the table below.
Part quality was determined by measuring the volume of the
thermoformed part, calculating the draw, and visually inspecting
the thermoformed part. The draw was calculated as the part volume
divided by the maximum part volume achieved in this set of
experiments (Examples A and B). The thermoformed part was visually
inspected for any blisters and the degree of blistering rated as
none (N), low (L), or high (H). The results below demonstrate that
these thermoplastic sheets with a glass transition temperature of
123.degree. C. cannot be thermoformed under the conditions shown
below, as evidenced by the inability to produce sheets having
greater than 95% draw and no blistering, without predrying the
sheets prior to thermoforming. TABLE-US-00039 Thermoforming
Conditions Part Quality Sheet Part Heat Time Temperature Volume
Blisters Example (s) (.degree. C.) (mL) Draw (%) (N, L, H) A 126
198 826 100 H B 111 188 822 100 H C 97 177 787 95 L D 74 166 161 19
L E 58 154 0 0 NA F 48 149 0 0 NA NA = not applicable. A value of
zero indicates that the sheet was not formed because it did not
pull into the mold (likely because it was too cold).
Example 25--Comparative Example
[1224] Sheets consisting of Teijin L-1250 polycarbonate were
produced using a 3.5 inch single screw extruder. A sheet was
extruded continuously, gauged to a thickness of 118 mil and then
various sheets were sheared to size. The glass transition
temperature was measured on one sheet and was 149.degree. C. Sheets
were then conditioned at 50% relative humidity and 60.degree. C.
for 4 weeks. The moisture level was measured to be 0.16 wt %.
Sheets were subsequently thermoformed into a female mold having a
draw ratio of 2.5:1 using a Brown thermoforming machine. The
thermoforming oven heaters were set to 70/60/60% output using top
heat only. Sheets were left in the oven for various amounts of time
in order to determine the effect of sheet temperature on the part
quality as shown in the table below. Part quality was determined by
measuring the volume of the thermoformed part, calculating the draw
and visually inspecting the thermoformed part. The draw was
calculated as the part volume divided by the maximum part volume
achieved in this set of experiments (Example A). The thermoformed
part was visually inspected for any blisters and the degree of
blistering rated as none (N), low (L), or high (H). The results
below demonstrate that these thermoplastic sheets with a glass
transition temperature of 149.degree. C. cannot be thermoformed
under the conditions shown below, as evidenced by the inability to
produce sheets having greater than 95% draw and no blistering,
without predrying the sheets prior to thermoforming. TABLE-US-00040
Thermoforming Conditions Part Quality Sheet Part Heat Time
Temperature Volume Blisters Example (s) (.degree. C.) (mL) Draw (%)
(N, L, H) A 152 216 820 100 H B 123 193 805 98 H C 113 191 179 22 H
D 106 188 0 0 H E 95 182 0 0 NA F 90 171 0 0 NA NA = not
applicable. A value of zero indicates that the sheet was not formed
because it did not pull into the mold (likely because it was too
cold).
It can be clearly seen from a comparison of the data in the above
relevant working examples that the polyesters of the present
invention offer a definite advantage over the commercially
available polyesters with regard to glass transition temperature,
density, slow crystallization rate, melt viscosity, and
toughness.
[1225] Example 24A coating composition was formed by mixing an
epoxy-functional polysiloxane with a UV curing additive. The
silicone used was available as General Electric 9300 silicone
release agent, and the UV curing agent used was General Electric
UV9380c. 50 grams of the silicone coating was stirred with 1 gram
of the UV curing agent until uniformly mixed. This coating was
applied to an amorphous extruded polyethylene terephthalate film.
The coated film was passed into a UV curing apparatus (American
Ultraviolet mini conveyorized UV cure system) at 50 feet per minute
at a power density setting of 200 watts per inch.
[1226] Additionally, extruded films of polyethylene, polystyrene,
PCTG, PETG and cellulose acetate were examined uncoated.
[1227] Biocompatibility was determined by measuring the adsorption
of protein from solution. The samples were first sonicated in water
for 10 minutes, followed by pretreatment in phosphate buffer for 24
hours. The samples were then immersed for 30 minutes in a 0.1 mg/mL
solution of bovine fibrinogen, removed and immersed for 30 minutes
in clean phosphate buffer solution. The samples were removed from
the buffer, rinsed with deionized water, and dried in vacuum for 24
hours. These samples were examined for surface atomic composition
using X-ray photoelectron spectroscopy (XPS). Because the
fibrinogen contains nitrogen and the substrate polymers do not, the
quantity of nitrogen detected at the surface is proportional to the
propensity for the surface to accumulate or adsorb proteins. It is
this adsorption of proteins at the surface that controls the
interaction of a biological system with a surface. TABLE-US-00041
Substrate % surface nitrogen PET 5.3 Copolyester "PETG" 6.6
Copolyester "PCTG" 5.6 Cellulose Acetate 4.7 Polypropylene 3.1
Silicone-coated PET 0.3
[1228] As seen from the results above, coatings of UV-cured
silicone materials on polymer substrates can substantially decrease
the amount of fibrinogen adsorbed onto surfaces as evidenced by a
lower indicated % surface nitrogen.
* * * * *