U.S. patent application number 09/846788 was filed with the patent office on 2001-10-11 for poly (vinyl alcohol) hydrogel.
Invention is credited to Ku, David N..
Application Number | 20010029399 09/846788 |
Document ID | / |
Family ID | 26723293 |
Filed Date | 2001-10-11 |
United States Patent
Application |
20010029399 |
Kind Code |
A1 |
Ku, David N. |
October 11, 2001 |
Poly (vinyl alcohol) hydrogel
Abstract
The present invention comprises a poly (vinyl alcohol) hydrogel
construct having a wide range of mechanical strengths for use as a
human tissue replacement. The hydrogel construct may comprise a
tissue scaffolding, a low bearing surface within a joint, or any
other structure which is suitable for supporting the growth of
tissue.
Inventors: |
Ku, David N.; (Atlanta,
GE) |
Correspondence
Address: |
LYON & LYON LLP
SUITE 4700
633 WEST FIFTH STREET
LOS ANGELES
CA
90071-2066
US
|
Family ID: |
26723293 |
Appl. No.: |
09/846788 |
Filed: |
May 1, 2001 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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09846788 |
May 1, 2001 |
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09271032 |
Mar 17, 1999 |
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6231605 |
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09271032 |
Mar 17, 1999 |
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08932029 |
Sep 17, 1997 |
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5981826 |
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60045875 |
May 5, 1997 |
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Current U.S.
Class: |
623/1.23 ;
606/108; 623/1.11; 623/1.35 |
Current CPC
Class: |
A61K 47/32 20130101;
A61L 27/16 20130101; A61L 2300/252 20130101; C08J 2329/04 20130101;
A61L 2300/432 20130101; A61K 9/06 20130101; A61L 2300/414 20130101;
A61L 27/3804 20130101; A61L 27/54 20130101; A61F 2/30756 20130101;
A61L 2300/254 20130101; A61K 9/0024 20130101; Y10S 623/901
20130101; A61L 2300/42 20130101; C08L 29/04 20130101; A61L 2300/256
20130101; A61L 27/52 20130101; A61L 2300/236 20130101; A61L 27/38
20130101; A61L 27/16 20130101; A61L 2300/426 20130101; C08J 3/075
20130101; A61L 2300/64 20130101 |
Class at
Publication: |
623/1.23 ;
623/1.11; 606/108; 623/1.35 |
International
Class: |
A61F 002/06; A61F
011/00 |
Claims
What is claimed is:
1. A biocompatible construct consisting essentially of a PVA
polymer and water, said construct having the following further
properties: a compressive modulus of elasticity between about 0.1
megaPascals and about 10 megaPascals, and a glass transition
temperature greater than about 40 degrees C.
2. The biocompatible construct of claim 1, said construct having
the following swelling properties: the material dimensions of said
construct change less than 20% by swelling following hydration by
submersion in an aqueous solution.
3. The biocompatible construct of claim 2 and further defined as
having its hydrated dimensions reduced by less than 20% following
submersion in an aqueous solution.
4. A biocompatible hydrogel joint resurfacing agent comprising: a
semicrystalline organic polymer; and water; said joint resurfacing
agent being further defined as having the following properties: a
water content greater than about 20%, by weight; a coefficient of
friction of less than 0.1; and a compressive modulus of elasticity
of between about 0.1 megaPascals and about 10 megaPascals.
5. The biocompatible hydrogel of claim 4, further defined as having
a water content of between about 20% and about 95% by weight.
6. A PVA construct consisting essentially of: a PVA polymer; and
saline; said construct having a compressive modulus of elasticity
of between about 0.5 megaPascals and about 10 megaPascals and a
glass transition temperature greater than 40.degree. C., said
construct being further defined as having been prepared according
to the following steps: pouring an aqueous PVA polymer mixture into
a mold; freezing and thawing said PVA polymer mixture within said
mold at least once to create an interlocking mesh between PVA
polymer molecules to create the semicrystalline organic hydrogel;
allowing for expansion of said PVA hydrogel within said mold.
7. A biocompatible hydrogel joint resurfacing agent comprising: a
semi-crystalline organic polymer; and a water content greater than
about 20% by weight; said hydrogel having a compressive modulus of
elasticity of between about 0.5 megaPascals and about 10
megaPascals and a glass transition temperature greater than
40.degree. C., said construct being further defined as having been
prepared according to the following steps: pouring an aqueous
semi-crystalline organic polymer mixture into a mold; freezing and
thawing said semi-crystalline organic polymer mixture within said
mold at least once to create an interlocking mesh between
semi-crystalline organic polymer molecules to create the
semi-crystalline organic polymer hydrogel; allowing for expansion
of said semi-crystalline organic polymer hydrogel, at least
partially within said mold.
8. The biocompatible hydrogel of claim 7 which further contains
eukaryotic cells.
9. The PVA hydrogel of claim 8, wherein said eukaryotic cells are
selected from the group consisting of: endothelial cells, aortic
endothelial cells, smooth muscle cells, fibroblasts, dermal
fibroblasts, and connective tissue cells.
10. The biocompatible hydrogel of claim 7 which further contains
radioisotopes.
Description
RELATED APPLICATIONS
[0001] This application claims a continuation priority to
application Ser. No. 09/271,032 filed on Mar. 17, 1999, which
issued as U.S. Pat. No. ________________ on ________________ and
which in turn claims priority to application Ser. No. 08/932,029,
filed on Sep. 17, 1997 which issued as U.S. Pat. No. 5,981,826 on
Nov. 9, 1999, and which claims priority to provisional application
Ser. No. 60/045,875, filed on May 5, 1997, which is incorporated
herein by reference in its entirety.
FIELD OF THE INVENTION
[0002] The present invention relates generally to hydrogel
materials. More specifically, the present invention relates to a
poly(vinyl alcohol) ("PVA") hydrogel.
DESCRIPTION OF THE PRIOR ART
[0003] Most tissues of the living body include a large weight
percentage of water. Therefore, in a selection of a prosthesis, a
hydrous polymer (hydrogel) is considered to be superior in
biocompatibility as compared to nonhydrous polymers. Although
hydrogels do less damage to tissues than nonhydrous polymers,
conventional hydrogels have historically included a serious defect
in that they are inferior in mechanical strength. For that reason,
the use of hydrogels has been extremely limited in the past.
[0004] Artisans have proposed a number of hardening means for
improving mechanical strength. Some hardening means include
treating the hydrogel with a cross-linking agent such as
formaldehyde, ethylaldehyde, glutaraldehyde, terephthalaldehyde or
hexamethylenediamine. Unfortunately, however, it is well known that
those treatments decrease the biocompatibility of the hydrogel
biomaterial. One example of a popular hydrogel which has been
proposed for use as a biomaterial is PVA.
[0005] Numerous references generally describe the process of
freezing and thawing PVA to create a hydrogel: Chu et al.,
Poly(vinyl alcohol) Cryogel: An Ideal Phantom Material for MR
Studies of Arterial Elasticity, Magnetic Resonance in Medicine, v.
37, pp. 314-319 (1997); Stauffer et al., Poly (vinyl alcohol)
hydrogels prepared by freezing-thawing cyclic processing, Polymer,
v.33, pp. 3932-3936 (1992); Lozinsky et al., Study of
Cryostructurization of polymer systems, Colloid & Polymer
Science, v. 264, pp. 19-24 (1986); Watase and Nishinari, Thermal
and rheological properties of poly (vinyl alcohol) hydrogels
prepared by repeated cycles of freezing and thawing, Makromol.
Chem., v. 189, pp. 871-880 (1988). The disclosure from these
references is hereby incorporated by reference.
[0006] Another such reference is U.S. Pat. No. 4,734,097, issued to
Tanabe et al. on Mar. 29, 1988 ("Tanabe"). Tanabe proposes the
construct of a molded hydrogel obtained by pouring an aqueous
solution containing not less than 6% by weight of a polyvinyl
alcohol which has a degree of hydrolysis not less than 97 mole
percent and an average polymerization degree of not less than 1,100
into a desired shape of a vessel or mold, freeze molding an aqueous
solution in a temperature lower than minus 5.degree. C., then
partially dehydrating the resulting molded product without thawing
it up to a percentage of dehydration not less than 5 weight
percent, and if required, immersing the partially hydrated molded
part into water to attain a water content thereof in the range of
45 to 95 weight percent.
[0007] The disadvantage to Tanabe et al. is that it necessarily
requires a step of dehydration in preparing the PVA hydrogel. There
are several disadvantages associated with the dehydration step.
First, the dehydration step adds additional time and capital
expense associated with machinery which must accomplish the
dehydration step. Additionally, dehydration may denature bioagents
included in the hydrogel.
[0008] Hyon et al., U.S. Pat. No. 4,663,358 is directed to
producing PVA hydrogels having a high tensile strength and water
content. However, this patent is not directed to hydrating the PVA
with water alone, but rather uses a mixture of water and an organic
solvent such as dimethyl sulfoxide (DMSO). DMSO is recognized as an
initiator of carcinogenicity. Residual amounts of organic solvents
in the resultant PVA hydrogel render such products undesirable for
biomedical applications, particularly where the hydrogel is to be
used for long term implants within the body.
[0009] Wood et al., U.S. Pat. No. 5,260,066 is directed to a
cryogel bandage having a therapeutic agent. The modulus of
elasticity properties of the product of Wood et al. are
insufficient to provide a joint replacement construct of the
present invention.
[0010] With the foregoing disadvantages of the prior art in mind,
it is an object of the present invention to provide a biocompatible
PVA hydrogel which includes a mechanical strength range sufficient
for a wide variety of applications as biomaterial.
[0011] It is another object of the present invention to provide a
method for producing the PVA hydrogel which precisely controls the
mechanical strength thereof, and which eliminates any dehydration
step prior to implantation.
[0012] Other objects, features and advantages of the present
invention will become apparent upon reading the following
specification.
SUMMARY OF THE INVENTION
[0013] Generally speaking, the present invention relates to a novel
poly(vinyl alcohol) ("PVA") hydrogel tissue replacement construct
and a process for making the construct.
[0014] More specifically, the present invention relates to a
non-dehydrated PVA hydrogel construct which is capable of being
molded into a number of shapes, and which is capable of retaining a
wide range of mechanical strengths for various applications.
[0015] The PVA hydrogel may comprise a PVA polymer starting
material in the form of a dry powder wherein the degree
polymerization of the PVA may range approximately 500 to 3,500. The
tissue replacement in accordance with the present invention may
include approximately 2 to approximately 40 parts by weight PVA and
approximately 98 to 60 parts by weight water. Additionally, the
hydrogel may include an isotonic saline solution substitute for
water to prevent osmotic imbalances between the tissue replacement
and surrounding tissues. The replacement may also include a number
of bioactive agents including, but not limited to, heparin, growth
factors, collagen crosslinking inhibitors such as
.beta.-aminopropeonitri- le (.beta.APN), matrix inhibitors,
antibodies, cytokines, integrins, thrombins, thrombin inhibitors,
proteases, anticoagulants and glycosaminoglycans.
[0016] A process in accordance with the present invention involves
mixing water with the PVA crystal to obtain a non-dehydrated PVA
hydrogel, thereby eliminating the dehydration step prior to
implantation. More specifically, the present invention involves
freezing and thawing the PVA/water mixture to create an
interlocking mesh between PVA polymer molecules to create the PVA
hydrogel. The freezing and thawing step may be performed at least
twice, with mechanical strength of the PVA hydrogel increasing each
time the freezing and thawing step is performed. The process may
include the further steps of pouring the PVA/water mixture into a
mold, freezing the mixture, and the thawing the mixture to obtain a
non-dehydrated construct. Additionally, the process may also
include the step of removing the construct from the mold, immersing
the construct in water, freezing the construct while immersed in
water and thawing the construct while immersed in water to increase
the mechanical strength of the construct. The process may also
include the steps of adding bioactive agents to the hydrogel.
[0017] Because it can be manufactured to be mechanically strong, or
to possess various levels of strength among other physical
properties, it can be adapted for use in many applications. The
hydrogel also has a high water content which provides desirable
properties in numerous applications. For example, the hydrogel
tissue replacement construct is especially useful in surgical and
other medical applications as an artificial material for replacing
and reconstructing soft tissues in humans and other mammals. Soft
tissue body parts which can be replaced or reconstructed by the
hydrogel include, but are not limited to, vascular grafts, heart
valves, esophageal tissue, skin, corneal tissue, cartilage,
meniscus, and tendon. Furthermore, the hydrogel may also serve as a
cartilage replacement for anatomical structures including, but not
limited to an ear or nose. The inventive hydrogel may also serve as
a tissue expander. Additionally, the inventive hydrogel may be
suitable for an implantable drug delivery device. In that
application, the rate of drug delivery to tissue will depend upon
hydrogel pore size and degree of intermolecular meshing resulting
from the freeze/thaw device. The rate of drug delivery increases
with the number of pores and decreases with an increasing degree of
intermolecular meshing from an increased number of freeze/thaw
cycles. The inventive hydrogel may consist essentially of a PVA
polymer and about 20% to about 95% water, by weight. The mechanical
and thermal properties of PVA hydrogel constructs, for biomedical
applications in particular, are important to the performance of the
constructs, as are the hydrogel's swelling properties and
coefficient of friction. The structures produced by the novel
process of this invention have advantageous properties in each of
these areas. The process of the present invention produces
crystallites in the PVA hydrogel polymer which leads to unique and
enhanced mechanical properties, thermal behavior and increased
fatigue strength.
[0018] The tensile properties of the PVA hydrogel of the present
invention may be characterized by its deformation behavior. The
freedom of motion of the PVA polymer of the present invention is
retained at a local level while the network structure produced by
the process of this invention prevents large-scale movements or
flow. Rubbery polymers tend to exhibit a lower modulus, or
stiffness, and extensibilities which are high. Glassy and
semi-crystalline polymers have higher moduli and lower
extensibilities. The tensile and compressive properties of the
construct of the present invention are reflected by a modulus of
elasticity of between about 0.1 and about 20 megaPascals, thus
producing a hydrogel having excellent strength and flexibility
characteristics.
[0019] In the liquid or melt state, a non-crystalline polymer
possesses enough thermal energy for long segments of each polymer
to move randomly, called Brownian motion. As the mixture cooled,
the temperature is eventually reached at which all long range
segmental motion ceases. This temperature at which segmental
motions ceases, which is a function of both the polymer material
and how it is processed, is called the glass transition
temperature. Experimentally, this glass transition temperature is
often defined by incrementally increasing the temperature of the
hydrogel until sequential reaction begins and energy is absorbed.
The glass transition properties of the PVA hydrogel construct
provided by the method of the present invention is greater than
about 40 degrees Celsius.
[0020] An integral part of the physical behavior of PVA hydrogel
constructs here disclosed is their swelling behavior in water,
because the process of this invention requires that the PVA be
immersed in water in order to yield the final, solvated network
structure. The thermodynamic swelling force is counter balanced by
the retractive force of the hydrogel structure and, in the process
of this invention, constrained by the mold in which the hydrogel is
placed. These retractive forces of the hydrogel are described by
the Flory rubber elasticity theory and its variations. Equilibrium
is reached, in water and at a particular temperature, when the if
thermodynamic swelling force is equal to the retractive force. The
swelling properties of the PVA hydrogel construct of this invention
are such that the dimensions of the construct are increased by
swelling by less than about 20%, and preferably less than about 5%,
when immersed in water. Alternatively, the shrinkage is
correspondingly less than 20%, and preferably less than about 5%.
When the PVA hydrogel of this invention is used in applications
such as biomedical applications, for example as a knee joint
resurfacing agent, low friction is desirable. The construct of the
present invention has a coefficient of friction of less than about
0.1. For a general description of the physical properties of
polymers and their properties see, Biomaterials Science an
Introduction to Materials in Medicine, Ratner, et al. (Academic
Press 1996), pp. 52-53 and 62.
[0021] The hydrogel is especially suitable for vascular grafts and
heart valve replacements, because the hydrogel is thromboresistant,
and because of the particular mechanical and physiological
requirements of vascular grafts when implanted into the body. The
hydrogel may also be used for contact lenses, as a covering for
wounds such as burns and abrasions, as a nerve bridge, as a
ureteral stent, and in other applications wherein a mechanically
strong material is preferred. Because of its low coefficient of
friction, the hydrogel may also be used as a coating to reduce
friction between surfaces, such as on a catheter.
[0022] Other objects, features and advantages of the present
invention will become apparent upon reading the following
specification, when taken in conjunction with the accompanying
examples.
[0023] Reference will now be made in detail to the description of
the invention. While the invention will be described in connection
with specific examples, there is no intent to limit it to the
embodiment or embodiments disclosed therein. On the contrary, the
intent is to cover all alternatives, modifications and equivalents
included within the spirit and scope of the invention as defined by
the appended claims.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0024] In a preferred embodiment, a process in accordance with the
present invention produces the hydrogel in a two stage process. In
the first stage a mixture of poly(vinyl alcohol) and water is
placed in a mold, and repeatedly frozen and thawed, in cycles,
until a suitable hydrogel is obtained. In a second stage, the
hydrogel is removed from the mold, placed in water, and undergoes
at least one other freeze-thaw cycle until desirable mechanical
properties are achieved. In the first stage, a series of sequential
steps is employed comprising: (i) mixing water with poly(vinyl
alcohol) to obtain a poly(vinyl alcohol)/water mixture; (ii)
freezing the mixture; (iii) thawing the mixture; and (iv) repeating
the freeze and thaw steps, as necessary, until a poly(vinyl
alcohol) hydrogel having the desired physical properties is
obtained. If necessary, the second stage may then be employed.
[0025] Poly(vinyl alcohol) useful for the invention is typically
obtained as a dry powder or crystal, and can vary based upon
several factors, including molecular weight, degree of
polymerization, and degree of saponification (or hydrolysis). The
molecular weight of the poly(vinyl alcohol) can vary, and can be
chosen depending upon the particular application envisioned for the
hydrogel. Generally, increasing the molecular weight of the
poly(vinyl alcohol) increases the tensile strength and tensile
stiffness, and thereby improves the properties of constructs such
as vascular grafts, wherein increased strength is desirable. In
other applications, such as a nerve bridge, lower molecular weight
poly(vinyl alcohol) can be employed because lower tensile strength
and lower tensile stiffness are desirable. Poly(vinyl alcohol)
having an average molecular weight of from about 11,000 to 500,000
is preferred for practicing the invention. Poly(vinyl alcohol)
having an average molecular weight of from about 85,000 to 186,000
is even more preferred for practicing the invention, especially
when producing vascular grafts, and poly(vinyl alcohol) having an
average molecular weight of from about 124,000 to 186,000 is
especially preferred.
[0026] The average degree of polymerization for preferred
poly(vinyl alcohol)s generally ranges from about 500 to 3500, and
poly(vinyl alcohol) having a degree of polymerization of from about
2700 to 3500 is especially preferred. Preferred poly(vinyl alcohol)
typically has a degree of saponification (or hydrolysis) in excess
of 80%, more preferred poly(vinyl alcohol) is saponified (or
hydrolyzed) in excess of about 98%, and even more preferred
poly(vinyl alcohol) is saponified (or hydrolyzed) in excess of
99%.
[0027] The water that is mixed with the poly(vinyl alcohol)
preferably undergoes deionization, reverse osmosis and ultra
filtered to minimize the potential for any contamination of the
poly(vinyl alcohol). The mixture is preferably prepared by mixing
from about 2 to about 40 parts by weight poly(vinyl alcohol) with
about 98 to 60 parts by weight water. The concentration of the
poly(vinyl alcohol) contributes to the stiffness of the hydrogel
and can thus be chosen depending upon the stiffness of the material
one desires to obtain. A more preferable mixture is obtained by
mixing from about 10 to about 30 parts poly(vinyl alcohol) with
from about 70 to about 90 parts by weight water, and an especially
preferred mixture is obtained by mixing about 25 parts poly(vinyl
alcohol) with about 75 parts by weight water. Isotonic saline (0.
9% weight to volume in water) or an isotonic buffered saline may be
substituted for water to prevent osmotic imbalances between the
material and surrounding tissues if the hydrogel is to be used as a
soft tissue replacement.
[0028] After the poly(vinyl alcohol) and water are mixed, it is
often necessary to process the mixture to ensure that the
poly(vinyl alcohol) is adequately solubilized. Suitable
solubilization processes are generally known in the art and
include, for example, heating the mixture, altering the pH of the
mixture, adding a solvent to the mixture, subjecting the mixture to
external pressure, or a combination of these processes. A preferred
method is to heat the mixture at a temperature of about 95.degree.
C.-120.degree. C., for a period of time not less than 15 minutes
and the one way of doing this, is an autoclave which also allows us
to sterilize the mixture before further processing.
[0029] After the mixture has been prepared, air bubbles that may
have become entrapped in the mixture should be removed. The
solution can be allowed to sit for a period of time, preferably at
an elevated temperature, to allow the air bubbles to rise out of
solution. The mixture can also be placed in a sterile vacuum
chamber for a short time to bring the bubbles out of solution. The
mixture can also be centrifuged at an elevated temperature to bring
the bubbles out of solution.
[0030] Once prepared, the mixture can be poured into one or more
pre-sterilized molds. If needed, the solution in the mold can be
allowed to sit upright, or subjected to a vacuum in a vacuum
chamber, to remove undesirable air bubbles. The shape and size of
the mold may be selected to obtain a hydrogel of any desired size
and shape. Vascular grafts, for example, can be produced by pouring
the poly(vinyl alcohol)/water mixture into an annular mold. The
size and dimensions of the mold can be selected based upon the
location for the graft in the body, which can be matched to
physiological conditions using normal tables incorporating limb
girth, activity level, and history of ischemia. Suitable annular
molds for producing vascular grafts would include Y-shaped molds,
which can be used to produce grafts having vascular branching. The
hydrogel can also be processed by cutting or otherwise forming the
hydrogel into the desired form after it has been produced. Although
not necessary, molds are preferably capped or sealed to prevent
dehydration and to preserve sterility. Typically, the mold is not
filled entirely with the solution in order to accommodate for the
expansion of the hydrogel during freezing.
[0031] Molds for practicing the invention can be comprised of many
suitable materials that will not react with the poly(vinyl alcohol)
solution, that will maintain integrity over the required
temperature range, and that will allow the hydrogel to be removed
without damaging the hydrogel. Suitable materials include but are
not limited to natural and synthetic resins, natural and synthetic
polymers (including those based upon polycarbonates, acrylates and
methacrylates, and poly(vinyl alcohol)), glass, steel, aluminum,
brass, and copper, among other materials. Outer molds that are
compliant and elastic result in a more complete gelling and better
physical properties than molds that are stiff. High pressure in the
frozen poly(vinyl alcohol) reduces the stiffness of the resulting
gel, and compliant molds reduce the pressure on the poly(vinyl
alcohol) while it is frozen. Preferred annular molds are
constructed from smooth stainless steel or poly(vinyl chloride)
tubes around stainless steel mandrels. More preferred annular
[0032] molds are constructed of compliant poly(vinyl chloride) or
other plastic tubes around stainless steel mandrels.
[0033] After the mixture has been poured into the mold, and the
mold has been sealed, it is frozen to a temperature preferably
below about -5.degree. C., and more preferably below about
-20.degree. C. The mixture should preferably be frozen for at least
1 hour, including freezing time, more preferably at least 4 hours,
and most preferably from about 4 to about 16 hours. In contrast to
methods cited in the prior art, no dehydration step is required,
and in a preferred embodiment dehydration is not employed because
of the importance of hydration to the final product.
[0034] After the mixture has been frozen, the temperature of the
mixture is raised and the mixture thawed. It is generally
preferable to raise the temperature to from about 5 to about
35.degree. C., and to thaw the solution at such temperature for a
period of time of about 1 hour or more, and more preferably at
least 4 hours, and most preferably from about 4 to about 16 hours,
including thawing time and time at such temperature. It is
especially preferable to raise the temperature to about 25.degree.
C., and to thaw the mixture at such temperature for about 12 hours.
Because the hydrogel is solubilized at higher temperatures, the
temperature of the mixture should not generally be raised above
about 45.degree. C.
[0035] After the mixture has been frozen and thawed once under the
foregoing conditions, the process may be repeated, although the
exact process conditions need not be repeated for each freeze/thaw
cycle. Generally, increasing the number of freeze/thaw cycles
increases the tensile strength and tensile stiffness of the
hydrogel, and can be implemented for applications such as vascular
grafts wherein higher strength and stiffness are desired. In other
applications, such as a nerve tube, lower numbers of freeze/thaw
cycles can be employed because lower tensile strength and lower
tensile stiffness are desirable. It is generally preferred to
repeat the freeze/thaw cycle from about 0 to about 15 times, and,
in vascular graft applications especially, more preferably from
about 3 to about 6 times. Most preferably, the freeze/thaw cycle is
repeated twice, for a total of three freeze/thaw cycles in the
first stage.
[0036] After the material has undergone the first stage of
freeze/thaw treatment it is carefully removed from the mold in
order to avoid damaging the material and immediately submerged in a
liquid bath, preferably of deionized, sterile water. The material
can be removed from the mold in either thawed or frozen state.
Moreover, the material can be removed from either part or the
entire mold. For example, it may be suitable to retain the mandrels
within the material if an annular mold is employed, to prevent the
material from deforming. The bath should be large enough so that
the material is immersed completely in water, and can be open or
closed, but preferably closed to maintain sterility.
[0037] The second stage involves further freeze/thaw treatment of
the molded material. After the mixture is immersed in water, it is
again subjected to one or more freeze/thaw cycles in the second
stage of the processing. Again, the conditions for each freeze/thaw
cycle in the second stage need not be identical. The mixture should
preferably be frozen and thawed from about 1 to about 15 times,
more preferably, especially for vascular graft applications, from 1
to 5 times, and most preferably 4 times, while the mixture is
submerged in the water. As in the first stage, increasing the
number of freeze/thaw cycles increases the tensile strength and
tensile stiffness, and the number of cycles can thus be selected
based upon the particular application that is planned for the
hydrogel.
[0038] The conditions under which the freeze/thaw cycles of the
second stage are carried out are generally comparable to the
conditions observed in carrying out the first stage. After the
mixture has undergone the second stage of freeze/thaw cycles, it is
ready for use.
[0039] The poly(vinyl alcohol) hydrogel of the present invention
can also comprise a 1.0 bioactive agent to lend to the hydrogel
suitable physiological properties for it to be used as a soft
tissue replacement. The bioactive agent can be chosen based upon
the particular application planned for the replacement, and the
particular physiological properties required of the replacement in
the application involved. Many such bioactive agents would be
released gradually from the hydrogel after implantation, and
thereby delivered in vivo at a controlled, gradual rate. The
hydrogel can thus act as a drug delivery vehicle. Other bioactive
agents can be incorporated in to the hydrogel in order to support
cellular growth and proliferation on the surface of the material.
Bioactive agents which can be included in the replacement include,
for example, growth factors, collagen crosslinking inhibitors such
as .beta.-aminopropeonitrile (.beta.APN) or cis-4-hydroxyproline,
matrix inhibitors, antibodies, cytokines, integrins, thrombins,
thrombin inhibitors, proteases, anticoagulants, and
glycosaminoglycans. Heparins are particularly suitable agents for
incorporating into vascular grafts, because of their anticoagulant
properties, and thus their ability to inhibit thrombosis on the
surface of the hydrogel.
[0040] In order to embed heparin or other bioactive agents into the
hydrogel of the present invention any of a pre-sterilized heparin
powder, aqueous heparin or aqueous heparin suspension can be mixed
into the starting sterile poly(vinyl alcohol)/water mixture. After
the heparin or other bioactive agent is incorporated into the
poly(vinyl alcohol)/water mixture, it is thermally processed along
with the poly(vinyl alcohol)/water mixture according to the process
described herein. Heparin and other bioactive agents can also be
introduced into the hydrogel by placing the hydrogel into a bath
containing an aqueous solution of the agent and allowing the agent
to diffuse into the hydrogel.
[0041] The concentration of the heparin or other bioactive agent in
the mixture may be selected for the particular application
involved. For heparin incorporation into a vascular graft,
concentrations will typically range from 1 unit/ml. to 1,000,000
units/ml. Lower concentrations will be employed to inhibit
coagulation on the graft surface, and higher concentrations will be
used where local infusion of heparin into the blood is desired to
inhibit thrombosis downstream of the graft, as described in Chen et
al., Boundary layer infusion of heparin prevents thrombosis and
reduces neointimal hyperplasia in venous polytetrafluoroethylene
grafts without systemic anticoagulation, J. Vascular Surgery, v.
22, pp., 237-247 (1995).
[0042] The hydrogel supports the proliferation of eukaryotic cell
cultures. Vascular cells such as endothelial cells, smooth muscle
cells, and fibroblasts and other connective tissue cells, can thus
be incorporated into the hydrogel. Human aortic endothelial cells
and human dermal fibroblasts are also compatible with the hydrogels
of the present invention. Hydrogels modified by such cell lines
are, in turn, especially well adapted for implantation into the
human body, and for use as soft tissue replacement parts in the
human body. Indeed, replacement parts modified by such cell lines
are better able to adapt and adjust to changing physical and
physiological conditions in the body, and thereby to prevent any
failure of the hydrogel which might otherwise occur. Hydrogels
modified by such cell lines are, in sum, especially well adapted
for implantation in the human body, and for use as replacement
parts in the human body. These cellular lines can be incorporated
into the hydrogel, after it has been produced, via standard cell
culture protocol generally known in the art. It is especially
effective to culture human aortic endothelial cells and human
dermal fibroblasts using direct topical seeding and incubation in
cell culture medium.
[0043] Besides the soft tissue replacement uses set forth for the
poly(vinyl alcohol) hydrogel, discussed above, the hydrogels of the
present invention can be used in any application in which
poly(vinyl alcohol) hydrogels are generally suitable, including as
an MR (magnetic resonance) quality control phantom, as an
ultrasound or radio frequency thermal therapy transmission pad, as
a substitute for an ice bag, as a denture base, and in other
medical applications.
[0044] Although the following examples set out specific parameters
for constructing a PVA hydrogel in accordance with the present
invention, the ordinarily skilled artisan will understand that
mechanical properties of the PVA hydrogel may be affected by one of
four factors. Those factors include: (1) weight percentage of the
respective constituents within the hydrogel (e.g. PVA polymer and
water); (2) the molecular weight of the PVA starting material; (3)
the number of freeze/thaw cycles; and (4) the duration of a freeze
cycle. It is also important to note that the freeze/thaw cycle
promotes an interlocking mesh or entanglement between molecules of
PVA to create the mechanical strength. This is different than the
traditional cross bits link accomplished by the above-referenced
cross linking agents which inevitably introduces a toxic agent into
the biomaterial, thus decreasing biocompatibility of materials
which utilize those cross linking agents.
EXAMPLE 1
[0045] A 15% by weight poly(vinyl alcohol) solution was prepared by
mixing 17.6 grams of poly(vinyl alcohol) polymer (124,000-186,000
Av. MW), 99+% saponification, in 100 ml of deionized, sterile
water. The mixture was placed in a loosely capped container, heated
and sterilized at 121.degree. C. and 17 p.s.i. in an autoclave for
about 15 minutes. The container was then sealed removed from the
autoclave and placed under a sterile ventilation hood. The mixture
was then stirred to ensure a homogenous solution. The mixture was
poured into sterile syringes, being careful not to generate air
bubbles. The poly(vinyl alcohol) solution was then injected
upwardly into stainless steel annular molds having stainless steel
mandrels. The outer tube of the annulus had an inner diameter of 8
mm which surrounded a 5 mm diameter mandrel. The time that the
solution was exposed to air was minimized in order to prevent
evaporation of water. The mold was designed to create a poly(vinyl
alcohol) hydrogel with approximately a 1.5 mm wall thickness, 10 cm
long, having a 5 mm inside diameter. The mold was sealed at both
ends using O-rings and rubber caps. Air space, equaling about 8% of
the volume of the mold was deliberately maintained in order to
allow for expansion while the aqueous solution froze.
[0046] The tube was then subjected to three (3) cycles of freezing
and thawing. In each of the cycles the tube was frozen by placing
it upright in a commercial freezer regulated at about -20.degree.
C., and allowing it to air cool for about 12 hours. The tube was
then thawed by removing the tube from the freezer and setting it
upright under ambient conditions. The tube was allowed to thaw for
about 12 hours before being returned to the freezer for another
cycle.
[0047] After the mixture had been frozen and thawed three times, it
was removed from the tube (under a sterile vacuum hood) and
immersed in a 50 ml, centrifuge vial containing 35 ml of deionized,
sterile water. There was obtained a translucent to clear, gummy,
weak material which was substantially unable to maintain its shape
outside of water or other liquid. The material was handled
carefully with forceps and immersed in water as quickly as
possible. The inner diameter of the material was preserved by
keeping the inner mandrel in place. The container was then sealed
and placed in a freezer at about -20.degree. C. The mixture was
kept in the freezer for about 12 hours, and then removed and
allowed to stand at room temperature for about 12 hours. The
freezing and thawing process was repeated once, thus considering
the three previous cycles within the mold, the mixture was
subjected to a total of five (5) cycles of freezing and
thawing.
[0048] The material obtained was opaque, elastic, and non-sticky,
with mechanical properties very similar to a native artery tissue.
The material was tested for mechanical strength according to
standards of the Association for the Advancement of Medical
Instrumentation and the American National Standards Institute,
published in Cardiovascular implants--Vascular Prosthesis,
ANSI/AAMI VP20-1994, section 8.3.3.3 (pressurized burst strength),
and Section 8.8 (suture retention strength). The material had a
burst pressure of about 540 mm Hg. Specifically, a 6-0 suture was
placed 2 mm from the edge of the graft and pulled at a rate of 150
mm/min until it pulled through the graft. The average peak pullout
load for the material a suture test was about 289 grams, which is
greater than the pullout loads reported in the literature for human
artery and vein. Finally, the tensile modulus of elasticity of the
material was measured to be approximately 4.0.times.10.sup.5
Pa.
EXAMPLE 2
[0049] A 25.9% by weight poly(vinyl alcohol) solution was prepared
by mixing poly(vinyl alcohol) polymer (124,000-186,000 Av. MW),
99+% saponification, in deionized, sterile water. As with Example
1, the mixture was placed in a loosely capped container, heated,
sealed removed from the autoclave, placed under a sterile
ventilation hood, stirred to ensure a homogenous solution, poured
into sterile syringes, and injected into the molds according to the
process of Example 1. In this example, however, the tube was then
subjected to ten (10) cycles of freezing and thawing. The
freeze/thaw cycles were similar to that of Example 1, except that
the sample was allowed to cool for about 24 hours for each
freeze/thaw cycle. The tube was then thawed by removing the tube
from the freezer and setting it upright under ambient conditions.
The tube was allowed to thaw for about 12 hours before being
returned to the freezer for another cycle. The resulting PVA
biomaterial was stiff and strong with a burst pressure of
approximately 1078 mm Hg.
EXAMPLE 3
[0050] A 15% by weight poly(vinyl alcohol) solution was prepared by
mixing poly(vinyl alcohol) polymer (89,000-98,000 Av. MW), 99+%
saponification, in deionized, sterile water in a manner
substantially identical with Example 1 except for the following
differences. As with Example 1, the mixture was placed in a loosely
capped container, heated, sealed removed from the autoclave, placed
under a sterile ventilation hood, stirred to ensure a homogenous
solution, poured into sterile syringes, and injected into the molds
according to the process of Example 1. In this example, however,
the tube was then subjected to five (5) cycles of freezing and
thawing. The freeze/thaw cycles were similar to that of Example 1,
in that each sample was allowed to cool for about 12 hours for each
freeze/thaw cycle. The resulting PVA biomaterial was soft with a
burst pressure of approximately 98 mm Hg.
EXAMPLE 4
[0051] A 25-30% by weight poly (vinyl alcohol) solution was
prepared by mixing poly (vinyl alcohol) polymer (124,000-186,000
Av. MW) in sterile water or saline (0.9% Na Cl) in a manner
substantially identical with Example 1 except for the following
differences. The mixture is heated at 95-100.degree. C. under
atmospheric pressure to bring the mixture to a uniform fluid. This
fluid is then poured into molds and frozen to -20.degree. C. for
four hours. Next, the material is thawed to 20.degree. C. This
freeze-thaw cycle is repeated until six cycles have been achieved.
The material is, at least partially, removed from the mold,
immersed, at least in part, and the freeze-thaw cycle is repeated
until four additional cycles have been achieved. As an alternative
to at least partially removing the material from the mold, the mold
may be partially filled with fluid mixture, thereby allowing for
expansion. The resultant PVA hydrogel construct is then ready for
packaging and sterilization. This process yields a material having
a modulus of elasticity (tensile or compression) which is greater
than 1.0 mPa. The % by weight and the MW of the PVA can be altered
to provide materials with a different modulus of elasticity
depending upon the particular medical application.
[0052] As demonstrated by the above-referenced examples, because
the PVA hydrogel can be manufactured to be mechanically strong, or
to possess various levels of strength among other physical
properties depending upon the weight percentage of the PVA starting
material with respect to other constituents in solution, freeze
time, the number of freeze/thaw cycles, and the freeze temperature.
As discussed above, the end product hydrogel also has a high water
content which provides desirable properties in numerous
applications and which prevents the denaturing of additives.
[0053] The hydrogel tissue replacement construct is especially
useful in surgical and other medical applications as an artificial
material for replacing and reconstructing soft tissues in humans
and other mammals. Soft tissue body parts which can be replaced or
reconstructed by the hydrogel include, but are not limited to,
vascular grafts, heart valves, esophageal tissue, skin, corneal
tissue, uretemal stents, nerve bridge, wound covering cartilage,
meniscus, and tendon. The hydrogel may be formed as an implantable
articulating surface for a load bearing joint, whereby the
articulating surface may be fixed to bone with screws, sutures, or
bioglue such as a collagenglue. Furthermore, the hydrogel may also
serve as a cartilage replacement for anatomical structures
including, but not limited to an ear or nose.
[0054] The inventive hydrogel may also serve as a tissue expander.
Additionally, the inventive hydrogel may be suitable for an
implantable drug delivery device. In that application, the rate of
drug delivery to tissue will depend upon hydrogel pore size and
degree of intermolecular meshing resulting from the freeze/thaw
cycles. The rate of drug delivery increases with the number of
pores and decreases with an increasing degree of intermolecular
meshing from an increased number of freeze/thaw cycles.
[0055] The hydrogel is especially suitable for vascular grafts and
heart valve replacements, because the hydrogel is thromboresistant,
and because of the particular mechanical and physiological
requirements of vascular grafts when implanted into the body. The
hydrogel may also be used for contact lenses, as a covering for
wounds such as burns and abrasions, and in other applications
wherein a mechanically strong material is preferred.
[0056] Throughout this application, various publications are
referenced. The disclosures of these publications in their
entireties are hereby incorporated by reference into this
application in order to more fully describe the state of the art to
which this invention pertains.
[0057] The foregoing description has been presented for purposes of
illustration and description. It is not intended to be exhaustive
or to limit the invention to the precise examples or embodiments
disclosed. Obvious modifications or variations are possible in
light of the above teachings. The embodiment or embodiments
discussed were chosen and described to provide the best
illustration of the principles of the invention and its practical
application to thereby enable one of ordinary skill in the art to
utilize the invention in various embodiments and with various
modifications as are suited to the particular use contemplated. All
such modifications and variations are within the scope of the
invention as determined by the appended claims when interpreted in
accordance with the breadth to which they are fairly and legally
entitled.
* * * * *