U.S. patent application number 12/271265 was filed with the patent office on 2009-03-12 for medical device with sponge coating for controlled drug release.
Invention is credited to W. Scott Andrus, Ni Ding.
Application Number | 20090069883 12/271265 |
Document ID | / |
Family ID | 22027138 |
Filed Date | 2009-03-12 |
United States Patent
Application |
20090069883 |
Kind Code |
A1 |
Ding; Ni ; et al. |
March 12, 2009 |
MEDICAL DEVICE WITH SPONGE COATING FOR CONTROLLED DRUG RELEASE
Abstract
The medical devices of the invention comprise an expandable
portion which is covered with a sponge coating for release of at
least one biologically active material. The sponge coating is made
of a non-hydrogel polymer having a plurality of voids. The device
can further include means for infusing or expelling the
biologically active material or drug into the voids. The drug is
delivered to the body lumen of a patient by expelling the drug and
inflating or expanding the expandable portion of the catheter or
device.
Inventors: |
Ding; Ni; (Plymouth, MN)
; Andrus; W. Scott; (Eden Prairie, MN) |
Correspondence
Address: |
KENYON & KENYON LLP
1500 K STREET N.W., SUITE 700
WASHINGTON
DC
20005
US
|
Family ID: |
22027138 |
Appl. No.: |
12/271265 |
Filed: |
November 14, 2008 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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10071400 |
Feb 7, 2002 |
7462165 |
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12271265 |
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09060071 |
Apr 14, 1998 |
6364856 |
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10071400 |
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Current U.S.
Class: |
623/1.42 ;
604/103.02 |
Current CPC
Class: |
A61L 2300/42 20130101;
A61M 25/104 20130101; A61M 2025/1075 20130101; A61L 31/16 20130101;
A61L 31/10 20130101; A61M 2025/1081 20130101; A61F 2250/0068
20130101; A61L 2300/236 20130101; A61F 2/86 20130101; A61L 2300/606
20130101; A61M 2025/105 20130101 |
Class at
Publication: |
623/1.42 ;
604/103.02 |
International
Class: |
A61F 2/82 20060101
A61F002/82; A61M 25/10 20060101 A61M025/10 |
Claims
1-46. (canceled)
47. A medical device having at least an expandable portion which is
insertable or implantable into a body lumen of a patient, wherein
at least a part of the expandable portion is covered with a coating
to form an exposed outermost surface for release of at least one
biologically active material; wherein the coating comprises a
non-hydrogel polymer having a plurality of voids; wherein the voids
contain at least one biologically active material; and wherein the
voids are formed by eluting a particulate material from the
polymer.
48. The device of claim 47 wherein the device is a catheter for
delivering the biologically active material and wherein the
expandable portion is expandable in response to expansion pressure
to substantially fill the cross-section of the lumen and engage the
tissue of the lumen.
49. The device of claim 48 wherein the expandable portion is a
balloon.
50. The device of claim 47 wherein the biologically active material
comprises an anti-proliferative agent.
51. The device of claim 47 wherein the biologically active material
comprises an agent selected from the group of taxol and its analogs
and derivatives.
52. The device of claim 47 wherein the non-hydrogel polymer
comprises an elastomeric polymer.
53. The device of claim 47 wherein the non-hydrogel polymer is
selected from the group of polyisobutylene and its copolymers.
54. A stent implantable into a body lumen of a patient, wherein at
least a part of the stent is covered with a coating to form an
exposed outermost surface for release of at least one biologically
active material; wherein the coating comprises a non-hydrogel
polymer having a plurality of voids; wherein the voids contain at
least one biologically active material; and wherein the voids are
formed by eluting a particulate material from the polymer.
55. The stent of claim 54 wherein the stent is a balloon-expandable
stent.
56. The stent of claim 54 wherein the stent is a self-expanding
stent.
57. The stent of claim 54 wherein the biologically active material
comprises an anti-proliferative agent.
58. The stent of claim 54 wherein the biologically active material
comprises an agent selected from the group of taxol and its analogs
and derivatives.
59. The stent of claim 54 wherein the non-hydrogel polymer
comprises an elastomeric polymer.
60. The stent of claim 54 wherein the non-hydrogel polymer is
selected from the group of polyisobutylene and its copolymers.
61. A method of delivering a biologically active material to a
desired location of a body lumen of a patient comprising: a)
forming a coating on a surface of an expandable portion of a
medical device for insertion or implantation into the body of a
patient, wherein the expandable portion has a surface which is
adapted for exposure to body tissue of the patient, the forming
done by: i) applying a composition comprising a non-hydrogel
polymer and a particulate material to the surface, and ii) exposing
the composition to a solvent to elute the particulate material from
the polymer to form a plurality of voids therein; b) loading the
coating with the biologically active material; c) delivering the
expandable portion of the medical device to a target location in
the body of the patient; and d) expanding the expandable portion of
the medical device at the target location to deliver the
biologically active material.
62. The method of claim 61 wherein the expandable portion of the
medical device comprises a balloon.
63. The method of claim 61 wherein the expandable portion of the
medical device comprises a stent.
64. The method of claim 61 wherein the biologically active material
comprises an anti-proliferative agent.
65. The method of claim 61 wherein the biologically active material
comprises an agent selected from the group of taxol and its analogs
and derivatives.
66. The method of claim 61 wherein the non-hydrogel polymer
comprises an elastomeric polymer.
Description
CROSS REFERENCE TO RELATED APPLICATION
[0001] This application is a Continuation of application Ser. No.
10/071,400 filed Feb. 7, 2002, which is a divisional of application
Ser. No. 09/060,071, filed Apr. 14, 1998 (now U.S. Pat. No.
6,364,856), both of which are incorporated herein by reference in
their entirety.
FIELD OF THE INVENTION
[0002] This invention relates generally to medical devices for
delivering a biologically active material to a desired location
within the body of a patient. More particularly, the invention is
directed to medical devices having a sponge coating comprising a
non-hydrogel polymer and a plurality of voids therein, optionally
formed by eluting a particulate material from the polymer. The
sponge coating is capable of being loaded with a drug, e.g.,
infusing or placing the drug into the voids, for release into the
body upon expansion of the coated portion of the medical
device.
BACKGROUND OF THE INVENTION
[0003] For certain diseases which are localized to a particular
part of the body, the systemic administration of drugs for the
treatment of these diseases may not be preferred because of the
inefficiencies associated with the indirect delivery of the drugs
to the afflicted area. Instead, it may be preferred that the drug
be directly applied to the diseased tissue. However, such localized
delivery of drugs to the walls of lumens, such as blood vessels and
ducts, can be problematic since lumens are involved in the
transport of body fluids, which tend to carry the drug away from
the afflicted area. Thus, there is a need for devices and methods
for the localized delivery of drugs to afflicted tissue, especially
body lumens.
[0004] A number of methods for delivering drugs to body lumens or
vessels involve the use of catheters having expandable portions,
such as a balloon, disposed on the catheter. For instance, U.S.
Pat. No. 5,304,121 to Sahatjian, PCT application WO 95/03083 to
Sahatjian et al. and U.S. Pat. No. 5,120,322 to Davis et al.
describe medical devices in which the exterior surface of the
device is coated with a swellable hydrogel polymer. A solution of a
drug to be delivered to the afflicted tissue is incorporated into
the hydrogel. The drug is held within the matrix of the hydrogel.
In the case where the medical device is a balloon catheter, the
drug is delivered by inserting the catheter into the body lumen and
expanding the coated balloon against the afflicted tissue of the
lumen to force the drug from the hydrogel into the tissue.
[0005] However, these hydrogel coated devices have certain
disadvantages. In particular, since the hydrogels are water-based,
only hydrophilic drugs can be effectively incorporated into the
hydrogels. Therefore, a number of useful hydrophobic biologically
active materials or drugs, such as dexamethasone, cannot be
suitably embedded into these hydrogels. Hence, there is a need for
a coating for a medical device which can effectively incorporate
such hydrophobic drugs in relatively large quantities.
[0006] Also, the application of the hydrogel coating to the balloon
usually involves multiple steps because most balloon materials are
hydrophobic so that a hydrogel usually has poor adhesion to the
balloon surface. Another disadvantage with hydrogels is that the
hydrogels will tend to be tacky or sticky when they are not fully
hydrated. When a hydrogel is not in its fully hydrated state, it
can stick to the surface of the packaging material or protection
sheath for the coated device and make the insertion or implantation
of the device difficult.
[0007] Moreover, even when prostheses having a drug containing
coating are implanted into the body, it is desirable to apply a
dose of the drug to the implantation site in addition to that
contained in the coating. Hence, there is a need for a device which
can deliver a prosthesis as well as a dose of the drug to the
implantation site.
SUMMARY OF THE INVENTION
[0008] These and other objectives are accomplished by the present
invention. To achieve the aforementioned objectives, we have
invented a medical device and a method for making and using such
device for the localized delivery of biologically active materials
as well as implanted prostheses to a patient.
[0009] The medical devices of the invention comprise an expandable
portion which is covered with a sponge coating for release of at
least one biologically active material. The sponge coating is made
of a non-hydrogel polymer having a plurality of voids. The void
space of the sponge coating is greater than about 60% of the volume
of the sponge coating. The device can further include means for
infusing the biologically active material or drug into the
voids.
[0010] In an embodiment of the invention, the device is a catheter
having an expandable portion which can be inflated or expanded by
inflation pressure to fill the cross-section of the body lumen and
engage the tissue of the body lumen. Upon expansion, the
biologically active material, which has been placed into the voids
of the sponge coating, is released into the body. The catheter can
also be capable of performing an angioplasty procedure at pressures
of greater than 6 atm and delivering an implantable prosthesis such
as a stent.
[0011] In another embodiment, the infusion means of the catheter
can further comprise an inflation lumen connected to a balloon with
pores. The balloon is filled with a biologically active material.
When the balloon is inflated, the biologically active material
infuses into the voids of the sponge coat and can be released into
the body lumen.
[0012] In yet another embodiment of the present invention, a
catheter has an expandable portion which comprises a reservoir
defined by a porous membrane. The porous membrane or film is used
to separate the sponge coating and the reservoir. The reservoir can
be connected to a reservoir lumen, thereby allowing the reservoir
to be filled with a biologically active material. Disposed about
the porous membrane of the reservoir is a sponge coat comprising a
non-hydrogel polymer having a plurality of voids formed by eluting
a particulate material from the polymer. Elution of the particulate
material means that such material becomes dissolved or suspended in
a surrounding solvent or fluid. The catheter can further include a
balloon disposed within the reservoir, wherein the balloon is
connected to an inflation lumen. When the balloon is expanded the
biologically active material of the reservoir is expelled or
"squeezed out" through the porous membrane and infused into the
voids of the sponge coat. Upon further expansion the biologically
active material is released from the sponge coating into the body
lumen.
[0013] Furthermore, in another embodiment of the invention the
medical device, which is coated with a sponge coating is an
expandable stent. The stent can be a self-expanding or balloon
expandable stent.
[0014] The devices of the present invention are prepared by
applying a sponge coating composition to a surface of an expandable
portion of a device. The sponge coating composition comprises a
non-hydrogel polymer dissolved in a solvent and an elutable
particulate material. After the sponge coating composition is
cured, it is exposed to a solvent, e.g., water, which causes the
particulate material to elute from the polymer leaving a sponge
coating having a plurality of voids therein. The sponge coating is
then exposed to a biologically active material to load the sponge
coating with such material. Such material may be loaded into the
coating by diffusion or other means.
DESCRIPTION OF THE DRAWINGS
[0015] FIGS. 1a and 1b depict cross-sectional views of an
embodiment of a drug delivery balloon catheter at the afflicted
area of the lumen in its unexpanded and expanded state,
respectively.
[0016] FIGS. 2a and 2b depict cross-sectional views of an
embodiment of a drug delivery catheter having a drug reservoir in
its unexpanded and expanded state, respectively.
[0017] FIG. 3 depicts a cross-sectional view of an embodiment of a
drug delivery catheter having a balloon containing a drug in its
expanded state.
[0018] FIGS. 4a and 4b depict a balloon expandable stent
prosthesis, in its unexpanded and expanded state respectively,
which is mounted on an expandable portion of a drug delivery
catheter.
[0019] FIGS. 5a and 5b depict a self-expanding stent prosthesis, in
its unexpanded and expanded state respectively, which is mounted on
an expandable portion of a drug delivery catheter.
[0020] FIGS. 6a-6c depict a method of preparing the sponge coating
for a balloon catheter.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0021] The medical devices suitable for the present invention
include those having at least an expandable portion. Such devices
include without limitation balloon catheters and perfusion
catheters, which are known to the skilled artisan.
[0022] An embodiment of the present invention is illustrated in
FIGS. 1a and 1b. FIG. 1a shows a catheter 1 being delivered to the
afflicted tissue 9 of a body lumen 8. The catheter 1 comprises an
expandable portion 2 having a balloon 3 disposed about the catheter
1. The outer surface of the balloon 3 is covered with a sponge
coating 4 of a non-hydrogel polymer having a plurality of voids 10
therein. A drug 5 is placed into the voids 10. An inflation lumen 6
is connected to the balloon 3 to fill the balloon 3 with fluid,
such as a liquid, or pressurized gas, and to expand the balloon 3.
A protective sheath 7 can be placed around the expandable portion 2
to prevent the drug 5 from being inadvertently released during
insertion of the catheter 1 into the body lumen 8.
[0023] FIG. 1b shows the catheter 1 in its deployed state. In FIG.
1b, the balloon 3 has been expanded to deliver the drug 5. The drug
5 is forced out of the sponge coating 4 by the expansion of the
balloon 3 against the body lumen 8. The drug 5 is thereby released
into the afflicted tissue 9 for treatment. In the case of an
expanded balloon, as shown in FIG. 1b, the expansion of the balloon
causes the sponge coating layer to become thinner, resulting in an
expulsion of the drug from the coating 4.
[0024] Another embodiment of the invention is depicted in FIGS. 2a
and 2b. The catheter 1 of this embodiment comprises an expandable
portion 2 having a reservoir 12 disposed about a balloon 3
connected to an inflation lumen 6. The reservoir 12 is connected to
a reservoir lumen 11 which can be used to fill the reservoir 12
with the drug 5. A porous membrane 13 defines the reservoir's outer
surface. A sponge coating 4--having voids 10 therein covers the
outer surface of the reservoir 12, i.e., outside the porous
membrane 13.
[0025] The drug 5 is delivered to the afflicted tissue 9 by filling
the reservoir 12 through the reservoir lumen 11 with a drug 5. As
the balloon 3 is expanded, drug 5 in the reservoir 12 passes or is
forced through the porous membrane 13 into the voids 10 of the
sponge coating 4. Additional expansion of the balloon 3 causes the
drug 5, which is in the sponge coating 4 to he released from the
sponge coating 4 into the afflicted tissue 9. A perfusion lumen can
be included in the catheter 1 to sustain the inflation of the
balloon 3, and infusion of the drug 5 into the sponge coating
4.
[0026] One of the advantages of infusing the sponge coating with
the drug is that such infusion maximizes the amount of drug
delivered to the afflicted area of the body lumen and reduces the
amount of drug which is lost to the lumen fluid, e.g., blood. Also,
infusion of the sponge coating with the drug permits the more even
distribution of the drug onto the afflicted lumen tissue without
damaging such tissue.
[0027] Also, a control unit (not shown) can be included to
synchronize the inflation of the balloon 3 with the delivery of the
drug 5 and the deflation of the balloon 3 with the infusion of the
drug 5 into the sponge coating 4. Such a control unit would
manipulate the timing of the infusion of the drug 5 into the sponge
coating 4 when the balloon 3 is being deflated instead of when it
is being inflated. Synchronization of-infusion with deflation
minimizes undesired "jetting" or excess release of large quantities
of drug 5 into the body lumen.
[0028] FIG. 3 illustrates yet another embodiment of a catheter 1 in
its expanded state wherein the balloon 3 and reservoir 12 of the
embodiment of FIGS. 2a and 2b are combined. In this embodiment,
drug 5 is placed into the balloon 3 through the inflation lumen 6
to expand the balloon 3. In other words by filling the balloon 3
with a fluid or composition containing the drug 5, the balloon 3 is
expanded. The force of expansion causes the drug 5 in the balloon 3
to infuse the drug 5 into the voids 10 of the sponge coating 4. By
expanding the balloon 3 further the drug 5 can be released from the
sponge coating 4 into afflicted tissue 9.
[0029] In addition, the catheters of the invention can be used to
deliver an implantable prosthesis such as an expandable stent. The
expandable stents which can be used in this invention include
self-expanding stents and balloon expandable stents. Examples of
self-expanding stents useful in the present invention are
illustrated in U.S. Pat. Nos. 4,655,771 and 4,954,126 issued to
Wallsten and 5,061,275 issued to Wallsten et al. Examples of
appropriate balloon-expandable stents are shown in U.S. Pat. No.
4,733,665 issued to Palmaz, U.S. Pat. No. 4,800,882 issued to
Gianturco and U.S. Pat. No. 4,886,062 issued to Wiktor.
[0030] Since the stent is implanted in the body, it can be covered
with a drug-releasing coating which provides long term delivery of
the drug. Generally, these coatings comprise a drug incorporated
into a polymeric material. Such drug-releasing coatings are
described in U.S. Pat. No. 5,464,650 to Berg et al.
[0031] The expandable stent may be formed from polymeric, metallic
and/or ceramic materials. Suitable polymeric materials include
without limitation poly-L-lactic acid, polycarbonate, and
polyethylene terephthalate.
[0032] FIGS. 4a and 4b show the delivery and deployment of a
balloon expandable stent 15 by a catheter 1 coated with a sponge
coating 4 having a drug 5 infused into the voids 10 of the sponge
coating 4. The stent 15 is disposed on the expandable portion 2 of
the catheter 1 for delivery as in FIG. 4a. The stent can also be
coated with a sponge coating, particularly one where the
particulate material is a drug. The stent 15 is implanted by
expanding the balloon 3 to force open the stent. Also, as shown in
FIG. 4b, when the stent 15 is deployed, expansion of the balloon 3
causes the drug 5 to infuse into the voids 10 of the sponge coating
4 and to be released into the body lumen 8.
[0033] The delivery and deployment of a self-expanding stent 16 by
a coated catheter 1 of the present invention is illustrated in
FIGS. 5a and 5b. In FIG. 5a, a sheath 7 is placed around the stent
16, which is disposed about the expandable portion 2 of the
catheter 1, to maintain the stent 16 in a contracted state for
delivery. After the stent 16 is placed to its implantation site,
the sheath 7 is withdrawn to deploy the self-expanding stent 16.
While or after the stent 16 expands, the balloon 3 is expanded to
further dilate the stent and release the drug 5 from the sponge
coating 4.
[0034] The following is a more detailed description of suitable
materials and methods useful in producing the sponge coatings of
the invention.
[0035] The non-hydrogel polymer(s) useful for forming the sponge
coating should be ones that are biostable, biocompatible,
particularly during insertion or implantation of the device into
the body and avoids irritation to body tissue. Non-hydrogel
polymers are polymers that when a drop of water is added on top of
a film of such polymer, the drop will not spread. Examples of such
polymers include without limitation polyurethanes, polyisobutylene
and its copolymers, silicones, and polyesters. Other suitable
polymers include polyolefins, polyisobutylene, ethylene-alphaolefin
copolymers, acrylic polymers and copolymers, vinyl halide polymers
and copolymers such as polyvinyl chloride, polyvinyl ethers such as
polyvinyl methyl ether, polyvinylidene halides such as
polyvinylidene fluoride and polyvinylidene chloride,
polyacrylonitrile, polyvinyl ketones, polyvinyl aromatics such as
polystyrene, polyvinyl esters such as polyvinyl acetate, copolymers
of vinyl-monomers, copolymers of vinyl monomers and olefins such as
ethylene-methyl methacrylate copolymers, acrylonitrile-styrene
copolymers, ABS resins, ethylene-vinyl acetate copolymers,
polyamides such as Nylon 66 and polycaprolactone, alkyd resins,
polycarbonales, polyoxyethylencs, polyimides, polyethers, epoxy
resins, polyurethanes, rayon-triacetate, cellulose, cellulose
acetate, cellulose butyrate, cellulose acetate butyrate,
cellophane, cellulose nitrate, cellulose propionate, cellulose
ethers, carboxymethyl cellulose, collagens, chitins, polylaetic
acid, polyglycolic acid, and polylactic acid-polyethylene oxide
copolymers.
[0036] Since the polymer is being applied to a part of the medical
device which undergoes mechanical challenges, e.g., expansion and
contraction, the polymers are preferably selected from elastomeric
polymers such as silicones (e.g. polysiloxanes and substituted
polysiloxanes), polyurethanes, thermoplastic elastomers, ethylene
vinyl acetate copolymers, polyolefin elastomers, polyisobutylene
and its copolymers and EPDM rubbers. The polymer is selected to
allow the coating to better adhere to the surface of the expandable
portion of the medical device when it is subjected to forces or
stress.
[0037] Furthermore, although the sponge coating can be formed by
using a single type of polymer, various combinations of polymers
can be employed. The appropriate mixture of polymers can be
coordinated with biologically active materials of interest to
produce desired effects when coated on a medical device in
accordance with the invention.
[0038] The elutable particulate materials which can be incorporated
into the polymer include without limitation polyethylene oxide,
polyethylene glycol, polyethylene oxide/polypropylene oxide
copolymers, polyhydroxyethyl methacrylate, polyvinylpyrrolidone,
polyacrylamide and its copolymers, salts, e.g., sodium chloride,
sugars, and elutable biologically active materials such as
heparin.
[0039] The amount of elutable particulate material that is
incorporated into the polymer should range from about 20% to 90% by
weight of the sponge coating and preferably, from about 50% to 90%.
The average particle size of the elutable material can range from
1-100 microns and preferably from about 2 to 15 microns.
[0040] The solvent that is used to form the mixture or slurry of
polymer and elutable particulate materials includes ones which can
dissolve the polymer into solution and do not alter or adversely
impact the therapeutic properties of the biologically active
material employed. Examples of useful solvents for silicone include
tetrahydrofuran (THF), chloroform and dichloromethane.
[0041] The composition of polymer and elutable particulate material
can be applied to the expandable portion of the medical device in a
variety of ways. For example, the composition can be spraycoated
onto the device or the device can be dipped into the composition.
One of skill in the art would be aware of methods for applying the
coating to the device. The thickness of the sponge coating can
range from about 25 .mu.m to 0.5 mm. Preferably, the thickness is
about 30 m to 100 .mu.m.
[0042] After the composition is applied to the device, it should be
cured to produce a polymer containing the particulate material and
to evaporate the solvent. Certain polymers, such as silicone, can
be cured at relatively low temperatures (e.g. room temperature) in
what is known as a room temperature vulcanization (RTV) process.
More typically, the curing/evaporation process involves higher
temperatures so that the coated device is heated in a oven.
Typically, the heating occurs at approximately 90.degree. C. or
higher for approximately 1 to 16 hours when silicone is used. For
certain coatings the heating may occur at temperatures as high as
150.degree. C. The time and temperature of heating will of course
vary with the particular polymer, drugs, and solvents used. One of
skill in the art is aware of the necessary adjustments to these
parameters.
[0043] To elute the particulate material from the polymer, a
solvent is used. The device can be soaked in the solvent to elute
the particulate materials. Other methods of eluting the particulate
are apparent to those skilled in the art.
[0044] The choice of the solvent depends upon the solubility of the
elutable particulate material in that solvent. For instance, for
water-soluble particulate materials such as heparin, water can be
used. For elutable particulate materials that can be dissolved in
organic solvents, such organic solvents can be used. Examples of
suitable solvents, without limitation, include ethanol, dimethyl
sulfoxide, etc.
[0045] After the particulate material is eluted from the polymer,
the medical device can be optionally sterilized. Depending upon the
nature of the drug used, sterilization of the device can occur
before or after the drug is loaded into the sponge coating. Methods
of sterilization are known in the art. For example, the devices can
be sterilized by exposure to gamma radiation at 2.5-3.5 Mrad or by
exposure to ethylene oxide.
[0046] As shown in FIGS. 6a-6c, in one method for making the sponge
coating 100, a mixture or slurry comprising a non-hydrogel polymer
101, an elutable particulate material 102 and a solvent is applied
to an expandable portion of the medical device. The device is then
exposed to an aqueous or organic solvent to elute the particulate
material 102 from the polymer 101 to form a plurality of voids 103
in the polymer 101. A biologically active material or drug 104 is
then loaded or placed into the voids 103 prior to delivery of the
drug 104 to the body.
[0047] To load the sponge coating with the biologically active
material or drug, a composition comprising the drug is applied to
the sponge coating. The drug can be loaded just prior to use of the
medical device. The drug can be loaded by immersing the sponge
coated portion of the device into the drug solution and allowing
the drug to diffuse into the voids of the sponge coating.
[0048] In order to place or infuse the drug into the sponge
coating, the drug should be dissolved or dispersed into a solvent.
The sponge coated portion of the device is then immersed into the
drug solution. Due to diffusion, the drug will enter the voids of
the sponge coating. After the solvent is permitted to evaporate, a
drug coated device is formed. The device can then be sterilized. If
the drug can not be sterilized, the physician can load the drug
just before the insertion or implantation procedure is
performed.
[0049] Alternatively, the medical device can be constructed such
that the drug can be infused from within the medical device as
described in the above-mentioned embodiments. For instance, the
catheter can include a drug reservoir whereby inflation of the
balloon causes the drug in the reservoir to infuse into the sponge
coating.
[0050] Furthermore, in another method for making the sponge
coating, the coating can be formed in viva, i.e., while the device,
which is coated with a polymer and an elutable particulate
material, is, inserted or implanted in the body. To prepare such a
coating, particulates, e.g., hydrophilic or lipophobic drug
particles are mixed with non-hydrogel polymeric materials. The
surface of the expandable portion of the medical device, such as a
balloon, is then coated with this mixture. After the coated device
is implanted or inserted into the body, body fluid which contacts
the coating permeates into the coating, thereby swelling the
coating and dissolving the drug. Some of the drug is then eluted
into the body fluid. When the balloon is inflated, additional drug
is forced out from the coating and directed to the afflicted body
lumen. In such a manner, a significant quantity of drug can be
delivered to the body lumen.
[0051] Suitable biologically active materials that can be used in
this invention include without limitation glucocorticoids (e.g.
dexamethasone, betamethasone), heparin, hirudin, angiopeptin,
aspirin, growth factors, antisense agents, anti-cancer agents,
anti-proliferative agents, oligonucicotides, and, more generally,
antiplalelet agents, anti-coagulant agents, antimitotic agents,
antioxidants, anti-metabolite agents, and anti-inflammatory agents
could be used. Antiplatelet agents can include drugs such as
aspirin and dipyridamole. Aspirin is classified as an analgesic,
antipyretic, anti-inflammatory and antiplatelet drug. Dipyridamole
is a drug similar to aspirin in that it has anti-platelet
characteristics. Dipyridamole is also classified as a coronary
vasodilator. Anticoagulant agents can include drugs such as
heparin, protamine, hirudin and tick anticoagulant protein.
Anti-cancer agents can induce drugs such as taxol, and its analogs
or derivatives, antioxidant agents can include probucol.
Anti-proliferative agents can include drugs such as amlodipine and
doxazosin. Anlimitotic agents and anlimelabolite agents can include
drugs such as methotrexate, azathioprine, vincristine, vinblastine,
5-fluorouracil, adriamycin and mutamycin. Antibiotic agents can
include penicillin, cefoxitin, oxacillin, tobramycin, and
gentamicin. Suitable antioxidants include probucol. Also, genes or
nucleic acids, or portions thereof can be used. Such genes or
nucleic acids can first be packaged in liposomes or nanoparticles.
Furthermore, collagen-synthesis inhibitors, such as tranilast, can
be used.
[0052] The description contained herein is for purposes of
illustration and not for purposes of limitation. Changes and
modifications may be made to the embodiments of the description and
still be within the scope of the invention. Furthermore, obvious
changes, modifications or variations will occur to those skilled in
the art. Also, all references cited above are incorporated herein,
in their entirety, for all purposes related to this disclosure.
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