Coating material and medical device system including same

Abstract

A coating material including a bio-absorbable cross-linked material and a cellular uptake inhibitor. The bio-absorbable cross-linked material includes two or more fatty acids cross-linked into a substantially random configuration by ester bonds. The coating material may be adhered to a medical device. A medical device system including a medical device and a coating is also included.

Claims

1. A coating material on an implantable medical device, wherein the coating material comprises: a bio-absorbable cross-linked material; a therapeutic agent; and a cellular uptake inhibitor; wherein the bio-absorbable cross-linked material comprises two or more fatty acids of a fish oil cross-linked into a random configuration by ester bonds to form a three-dimensional network of a gel.

2. The coating material of claim 1, wherein the cellular uptake inhibitor comprises alpha-tocopherol.

3. The coating material of claim 1, wherein the two or more fatty acids are omega-3 fatty acids.

4. The coating material of claim 3, wherein the two or more omega-3 fatty acids are selected from the group consisting of eicosapentaenoic acid (EPA), docosahexaenoic acid (DHA) and -linolenic acid (ALA).

5. The coating material of claim 1, wherein the medical device is a stent.

6. The coating material of claim 5, wherein the stent is formed of one or more substance selected from the group of substances consisting of stainless steel, nitinol alloy, nickel alloy, titanium alloy, cobalt-chromium alloy, ceramics, metals, plastics, or polymers.

7. The coating material of claim 1, wherein the medical device comprises a pre-treatment, and wherein the pre-treatment improves the adhesion of the coating to the medical device.

8. The coating material of claim 1, wherein the therapeutic agent comprises one or more agents selected from the group of agents consisting of antioxidants, anti-inflammatory agents, anti-coagulant agents, drugs to alter lipid metabolism, anti-proliferatives, anti-neoplastics, anti-fibrotics, immunosuppressive, tissue growth stimulants, functional protein/factor delivery agents, anti-infective agents, imaging agents, anesthetic agents, chemotherapeutic agents, tissue absorption enhancers, anti-adhesion agents, germicides, antiseptics, proteoglycans, gene delivery, polynucleotides, analgesics, prodrugs and polysaccharides.

9. The coating material of claim 1, wherein the coating material is configured to effect controlled release of the therapeutic agent.

10. The coating material of claim 1, wherein the two or more fatty acids cross-linked into a substantially random configuration by ester bonds are formed by heat curing or UV curing.

11. The coating material of claim 1, wherein the therapeutic agent comprises an agent selected from the group consisting of cerivastatin, cilostazol, fluvastatin, lovastatin, paclitaxel, pravastatin, rapamycin, and simvastatin.

12. The coating material of claim 1, wherein the coating material inhibits neointimal growth.

13. The coating material of claim 1, wherein the coating material promotes endothelialization.

14. The coating material of claim 1, wherein the gel is a flexible gel structure.

15. The coating material of claim 1, wherein the therapeutic agent remains pharmacologically effective after the coating material is cured.

16. The coating material of claim 1, wherein the two or more fatty acids cross-linked into a random configuration by ester bonds are formed by curing without the addition of external crosslinking agents.

17. The coating material of claim 1, wherein upon implantation in a patient there is no break-down of the coating into sub parts and substances which induce an inflammatory response.

18. A medical system comprising: a medical device; and a coating disposed on the medical device, wherein the coating includes a bio-absorbable cross-linked material; and a cellular uptake inhibitor; wherein the bio-absorbable cross-linked material comprises two or more omega-3 fatty acids cross-linked into a random configuration by ester bonds to form a non-polymeric three-dimensional network.

19. The medical system of claim 18, further comprising a therapeutic agent mixed in with the bio-absorbable cross-linked material and the cellular uptake inhibitor.

20. The medical system of claim 18, wherein the two or more omega-3 fatty acids are derived from fish oil.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

(1) The aforementioned features and advantages, and other features and aspects of the present invention, will become better understood with regard to the following description and accompanying drawings, wherein:

(2) FIG. 1 is a diagrammatic illustration of a medical device, according to one embodiment of the present invention;

(3) FIG. 2 is a cross-sectional view of the medical device in accordance with one aspect of the present invention;

(4) FIG. 3 is a cross-sectional view of the medical device in accordance with another aspect of the present invention;

(5) FIG. 4 is a flow chart illustrating a method of making the coated medical device of the present invention, in accordance with one embodiment of the present invention;

(6) FIG. 5 is a flow chart illustrating a variation of the method of FIG. 4, in accordance with one embodiment of the present invention;

(7) FIG. 6 is a flow chart illustrating another variation of the method of FIG. 4, in accordance with one embodiment of the present invention;

(8) FIG. 7 is a flow chart illustrating another variation of the method of FIG. 4, in accordance with one embodiment of the present invention;

(9) FIG. 8 is a diagrammatic illustration of a coated medical device in accordance with one embodiment of the present invention;

(10) FIG. 9 is a graph depicting the amount of methylprednisone released over time in water from a coated stent prepared in accordance with Example 17;

(11) FIG. 10 is a graph depicting the amount of methylprednisone released over time in water from a coated stent prepared in accordance with Example 18;

(12) FIG. 11 is a graph depicting the cumulative amount of cilostazol released over time in water from three individual coated stents prepared in accordance with Examples 15, 16 and 19;

(13) FIG. 12 is a graph depicting the percentage of paclitaxel released over time in a 35% solution of acetonitrile/water from a coated stent prepared in accordance with Example 21; and

(14) FIG. 13 is a graph comparing the amount of rapamycin released over time in a phosphate buffered saline (PBS) solution from high dose, low dose and high dose extended-release coated stents prepared in accordance with the present invention relative to a known stent.

DETAILED DESCRIPTION

(15) An illustrative embodiment of the present invention relates to the provision of a coating on an implantable medical device. The coating includes a bio-absorbable carrier component. In addition to the bio-absorbable carrier component, a therapeutic agent component can also be provided. The coated medical device is implantable in a patient to effect controlled delivery of the coating to the patient.

(16) As utilized herein, the term bio-absorbable generally refers to having the property or characteristic of being able to penetrate the tissue of a patient's body. In certain embodiments of the present invention bio-absorption occurs through a lipophilic mechanism. The bio-absorbable substance is soluble in the phospholipid bi-layer of cells of body tissue, and therefore impacts how the bio-absorbable substance penetrates into the cells.

(17) It should be noted that a bio-absorbable substance is different from a biodegradable substance. Biodegradable is generally defined as capable of being decomposed by biological agents, or capable of being broken down by microorganisms or biological processes, in a manner that does not result in cellular uptake of the biodegradable substance. Biodegradation thus relates to the breaking down and distributing of a substance through the patient's body, verses the penetration of the cells of the patient's body tissue. Biodegradable substances can cause inflammatory response due to either the parent substance or those formed during breakdown, and they may or may not be absorbed by tissues.

(18) The phrase controlled release generally refers to the release of a biologically active agent in a predictable manner over the time period of weeks or months, as desired and predetermined upon formation of the biologically active agent on the medical device from which it is being released. Controlled release includes the provision of an initial burst of release upon implantation, followed by the predictable release over the aforementioned time period.

(19) With regard to the aforementioned oils, it is generally known that the greater the degree of unsaturation in the fatty acids the lower the melting point of a fat, and the longer the hydrocarbon chain the higher the melting point of the fat. A polyunsaturated fat, thus, has a lower melting point, and a saturated fat has a higher melting point. Those fats having a lower melting point are more often oils at room temperature. Those fats having a higher melting point are more often waxes or solids at room temperature. Therefore, a fat having the physical state of a liquid at room temperature is an oil. In general, polyunsaturated fats are liquid oils at room temperature, and saturated fats are waxes or solids at room temperature.

(20) Polyunsaturated fats are one of four basic types of fat derived by the body from food. The other fats include saturated fat, as well as monounsaturated fat and cholesterol. Polyunsaturated fats can be further composed of omega-3 fatty acids and omega-6 fatty acids. Under the convention of naming the unsaturated fatty acid according to the position of its first double bond of carbons, those fatty acids having their first double bond at the third carbon atom from the methyl end of the molecule are referred to as omega-3 fatty acids. Likewise, a first double bond at the sixth carbon atom is called an omega-6 fatty acid. There can be both monounsaturated and polyunsaturated omega fatty acids.

(21) Omega-3 and omega-6 fatty acids are also known as essential fatty acids because they are important for maintaining good health, despite the fact that the human body cannot make them on its own. As such, omega-3 and omega-6 fatty acids must be obtained from external sources, such as food. Omega-3 fatty acids can be further characterized as containing eicosapentaenoic acid (EPA), docosahexanoic acid (DHA), and alpha-linolenic acid (ALA). Both EPA and DHA are known to have anti-inflammatory effects and wound healing effects within the human body.

(22) Oil that is hydrogenated becomes a waxy solid. Attempts have been made to convert the polyunsaturated oils into a wax or solid to allow the oil to adhere to a device for a longer period of time. One such approach is known as hydrogenation, which is a chemical reaction that adds hydrogen atoms to an unsaturated fat (oil) thus saturating it and making it solid at room temperature. This reaction requires a catalyst, such as a heavy metal, and high pressure. The resultant material forms a non-cross-linked semi-solid. Hydrogenation can reduce or eliminate omega-3 fatty acids, and any therapeutic effects (both anti-inflammatory and wound healing) they offer.

(23) In addition, some curing methods have been indicated to have detrimental effects on the therapeutic agent combined with the omega-3 fatty acid, making them partially or completely ineffective. As such, oils, and more specifically oils containing omega-3 fatty acids, have been utilized as a delivery agent for the short term uncontrolled release of a therapeutic agent, so that minimal or no curing is required. However, there are no known uses of oils containing omega-3 fatty acids for combination with a therapeutic agent in a controlled release application that makes use of the therapeutic benefits of the omega-3 fatty acids. Further, some heating of the omega-3 fatty acids to cure the oil can lessen the total therapeutic effectiveness of the omega-3 fatty acids, but not eliminate the therapeutic effectiveness. One characteristic that can remain after certain curing by heating methods is the non-inflammatory response of the tissue when exposed to the cured material. As such, an oil containing omega-3 fatty acids can be heated for curing purposes, and still maintain some or even a substantial portion of the therapeutic effectiveness of the omega-3 fatty acids. In addition, although the therapeutic agent combined with the omega-3 fatty acid and cured with the omega-3 fatty acid can be rendered partially ineffective, the portion remaining of the therapeutic agent can, in accordance with the present invention, maintain pharmacological activity and in some cases be more effective than an equivalent quantity of agent delivered with other coating delivery agents. Thus, if for example, 80% of a therapeutic agent is rendered ineffective during curing, the remaining 20% of therapeutic agent, combined with and delivered by the coating can be efficacious in treating a medical disorder, and in some cases have a relatively greater therapeutic effect than the same quantity of agent delivered with a polymeric or other type of coating.

(24) For long term controlled release applications, polymers, as previously mentioned, have been utilized in combination with a therapeutic agent. Such a combination provides a platform for the controlled long term release of the therapeutic agent from a medical device. However, polymers have been determined to themselves cause inflammation in body tissue. Therefore, the polymers often must include at least one therapeutic agent that has an anti-inflammatory effect to counter the inflammation caused by the polymer delivery agent. In addition, patients that received a polymer-based implant must also follow a course of long term systemic anti-platelet therapy, on a permanent basis, to offset the thrombogenic properties of the non-absorbable polymer. A significant percentage of patients that receive such implants are required to undergo additional medical procedures, such as surgeries (whether related follow-up surgery or non-related surgery) and are required to stop their anti-platelet therapy. This can lead to a thrombotic event, such as stroke, which can lead to death. Use of the inventive coating described herein can negate the necessity of anti-platelet therapy, and the corresponding related risks described, because there is no thrombogenic polymer reaction to the coating.

(25) FIGS. 1 through 13, wherein like parts are designated by like reference numerals throughout, illustrate an example embodiment of a coated medical device according to the present invention. Although the present invention will be described with reference to the example embodiments illustrated in the figures, it should be understood that many alternative forms can embody the present invention. One of ordinary skill in the art will additionally appreciate different ways to alter the parameters of the embodiments disclosed, such as the size, shape, or type of elements or materials, in a manner still in keeping with the spirit and scope of the present invention.

(26) FIG. 1 illustrates a stent 10 in accordance with one embodiment of the present invention. The stent 10 is representative of a medical device that is suitable for having a coating applied thereon to effect a therapeutic result. The stent 10 is formed of a series of interconnected struts 12 having gaps 14 formed therebetween. The stent 10 is generally cylindrically shaped. Accordingly, the stent 10 maintains an interior surface 16 and an exterior surface 18.

(27) One of ordinary skill in the art will appreciate that the illustrative stent 10 is merely exemplary of a number of different types of stents available in the industry. For example, the strut 12 structure can vary substantially. The material of the stent can also vary from a metal, such as stainless steel, Nitinol, nickel, and titanium alloys, to cobalt chromium alloy, ceramic, plastic, and polymer type materials. One of ordinary skill in the art will further appreciate that the present invention is not limited to use on stents. Instead, the present invention has application on a wide variety of medical devices. For purposes of clarity, the following description will refer to a stent as the exemplar medical device. The terms medical device and stent are interchangeable with regard to the applicability of the present invention. Accordingly, reference to one or another of the stent, or the medical device, is not intended to unduly limit the invention to the specific embodiment described.

(28) FIG. 2 illustrates one example embodiment of the stent 10 having a coating 20 applied thereon in accordance with the present invention. FIG. 3 is likewise an alternative embodiment of the stent 10 having the coating 20 also applied thereon. The coating 20 is applied to the medical device, such as the stent 10, to provide the stent 10 with different surface properties, and also to provide a vehicle for therapeutic applications.

(29) In FIG. 2, the coating 20 is applied on both the interior surface 16 and the exterior surface 18 of the strut 12 forming the stent 10. In other words, the coating 20 in FIG. 2 substantially encapsulates the struts 12 of the stent 10. In FIG. 3, the coating 20 is applied only on the exterior surface 18 of the stent 10, and not on the interior surface 16 of the stent 10. The coating 20 in both configurations is the same coating; the difference is merely the portion of the stent 10 that is covered by the coating 20. One of ordinary skill in the art will appreciate that the coating 20 as described throughout the Description can be applied in both manners shown in FIG. 2 and FIG. 3, in addition to other configurations such as, partially covering select portions of the stent 10 structure. All such configurations are described by the coating 20 reference.

(30) In accordance with embodiments of the present invention, the stent 10 includes the coating 20, which is bio-absorbable. The coating 20 has a bio-absorbable carrier component, and can also include a therapeutic agent component that can also be bio-absorbable. When applied to a medical device such as a stent 10, it is often desirable for the coating to inhibit or prevent restenosis. Restenosis is a condition whereby the blood vessel experiences undesirable cellular remodeling after injury. When a stent is implanted in a blood vessel, and expanded, the stent itself may cause some injury to the blood vessel. The treated vessel typically has a lesion present which can contribute to the inflammation and extent of cellular remodeling. The end result is that the tissue has an inflammatory response to the conditions. Thus, when a stent is implanted, there is often a need for the stent to include a coating that inhibits inflammation, or is non-inflammatory, and prevents restenosis. These coatings have been provided using a number of different approaches as previously described in the Background. However, none of the prior coatings have utilized a bio-absorbable carrier component to create a bio-absorbable coating with suitable non-inflammatory properties for controlled release of a therapeutic agent.

(31) In accordance with one embodiment of the present invention, the bio-absorbable carrier component is in the form of a naturally occurring oil. An example of a naturally occurring oil is fish oil or cod liver oil. A characteristic of the naturally occurring oil is that the oil includes lipids, which contributes to the lipophilic action described later herein, that is helpful in the delivery of therapeutic agents to the cells of the body tissue. In addition, the naturally occurring oil includes omega-3 fatty acids in accordance with several embodiments of the present invention. As previously described, omega-3 fatty acids and omega-6 fatty acids are known as essential fatty acids. Omega-3 fatty acids can be further characterized as eicosapentaenoic acid (EPA), docosahexanoic acid (DHA), and alpha-linolenic acid (ALA). Both EPA and DHA are known to have anti-inflammatory effects and wound healing effects within the human body.

(32) In further detail, the term bio-absorbable generally refers to having the property or characteristic of being able to penetrate the tissues of a patient's body. In example embodiments of the present invention, the bio-absorbable coating contains lipids, many of which originate as triglycerides. It has previously been demonstrated that triglyceride products such as partially hydrolyzed triglycerides and fatty acid molecules can integrate into cellular membranes and enhance the solubility of drugs into the cell. Whole triglycerides are known not to enhance cellular uptake as well as partially hydrolyzed triglyceride, because it is difficult for whole triglycerides to cross cell membranes due to their relatively larger molecular size. Vitamin E compounds can also integrate into cellular membranes resulting in decreased membrane fluidity and cellular uptake.

(33) It is also known that damaged vessels undergo oxidative stress. A coating containing an antioxidant such as alpha-tocopherol may aid in preventing further damage by this mechanism.

(34) Compounds that move too rapidly through a tissue may not be effective in providing a sufficiently concentrated dose in a region of interest. Conversely, compounds that do not migrate in a tissue may never reach the region of interest. Cellular uptake enhancers such as fatty acids and cellular uptake inhibitors such as alpha-tocopherol can be used alone or in combination to provide an effective transport of a given compound to a given region or location. Both fatty acids and alpha-tocopherol are accommodated by the coating of the present invention described herein. Accordingly, fatty acids and alpha-tocopherol can be combined in differing amounts and ratios to contribute to a coating in a manner that provides control over the cellular uptake characteristics of the coating and any therapeutic agents mixed therein.

(35) It should further be emphasized that the bio-absorbable nature of the carrier component and the resulting coating (in the instances where a bio-absorbable therapeutic agent component is utilized) results in the coating 20 being completely absorbed over time by the cells of the body tissue. There are no substances in the coating, or break down products of the coating, that induce an inflammatory response. In short, the coating 20 is generally composed of fatty acids, including in some instances omega-3 fatty acids, bound to triglycerides, potentially also including a mixture of free fatty acids and vitamin E. The triglycerides are broken down by lipases (enzymes) which result in free fatty acids that can than be transported across cell membranes. Subsequently, fatty acid metabolism by the cell occurs to metabolize any substances originating with the coating. The bio-absorbable nature of the coating of the present invention thus results in the coating being absorbed, leaving only an underlying delivery or other medical device structure. There is no foreign body response to the bio-absorbable carrier component, including no inflammatory response. The modification of the oils from a more liquid physical state to a more solid, but still flexible, physical state is implemented through the curing process. As the oils are cured, especially in the case of fatty acid-based oils such as fish oil, cross-links form creating a gel. As the curing process is performed over increasing time durations and/or increasing temperature conditions, more cross-links form transitioning the gel from a relatively liquid gel to a relatively solid-like, but still flexible, gel structure.

(36) As previously mentioned, the coating can also include a therapeutic agent component. The therapeutic agent component mixes with the bio-absorbable carrier component as described later herein. The therapeutic agent component can take a number of different forms including but not limited to anti-oxidants, anti-inflammatory agents, anti-coagulant agents, drugs to alter lipid metabolism, anti-proliferatives, anti-neoplastics, tissue growth stimulants, functional protein/factor delivery agents, anti-infective agents, anti-imaging agents, anesthetic agents, therapeutic agents, tissue absorption enhancers, anti-adhesion agents, germicides, antiseptics, proteoglycans, GAG's, gene delivery (polynucleotides), polysaccharides (e.g., heparin), anti-migratory agents, pro-healing agents, ECM/protein production inhibitors, analgesics, prodrugs, and any additional desired therapeutic agents such as those listed in Table 1 below.

(37) TABLE-US-00001 TABLE 1 CLASS EXA MPLES Antioxidants Alpha-tocopherol, lazaroid, probucol, phenolic antioxidant, resveretrol, AGI-1067, vitamin E Antihypertensive Diltiazem, nifedipine, verapamil Agents Antiinflammatory Glucocorticoids (e.g. dexamethazone, Agents methylprednisolone), leflunomide, NSAIDS, ibuprofen, acetaminophen, hydrocortizone acetate, hydrocortizone sodium phosphate, macrophage-targeted bisphosphonates Growth Factor Angiopeptin, trapidil, suramin Antagonists Antiplatelet Agents Aspirin, dipyridamole, ticlopidine, clopidogrel, GP IIb/IIIa inhibitors, abcximab Anticoagulant Bivalirudin, heparin (low molecular weight and Agents unfractionated), wafarin, hirudin, enoxaparin, citrate Thrombolytic Alteplase, reteplase, streptase, urokinase, TPA, Agents citrate Drugs to Alter Fluvastatin, colestipol, lovastatin, atorvastatin, Lipid Metabolism amlopidine (e.g. statins) ACE Inhibitors Elanapril, fosinopril, cilazapril Antihypertensive Prazosin, doxazosin Agents Antiproliferatives Cyclosporine, cochicine, mitomycin C, sirolimus and Antineoplastics micophenonolic acid, rapamycin, everolimus, tacrolimus, paclitaxel, QP-2, actinomycin, estradiols, dexamethasone, methatrexate, cilostazol, prednisone, cyclosporine, doxorubicin, ranpirnas, troglitzon, valsarten, pemirolast, C-MYC antisense, angiopeptin, vincristine, PCNA ribozyme, 2-chloro-deoxyadenosine Tissue growth Bone morphogeneic protein, fibroblast growth stimulants factor Promotion of Alcohol, surgical sealant polymers, polyvinyl hollow organ particles, 2-octyl cyanoacrylate, hydrogels, occlusion or collagen, liposomes thrombosis Functional Protein/ Insulin, human growth hormone, estradiols, nitric Factor delivery oxide, endothelial progenitor cell antibodies Second messenger Protein kinase inhibitors targeting Angiogenic Angiopoetin, VEGF Anti-Angiogenic Endostatin Inhibitation of Halofuginone, prolyl hydroxylase inhibitors, Protein Synthesis/ C-proteinase inhibitors ECM formation Antiinfective Penicillin, gentamycin, adriamycin, cefazolin, Agents amikacin, ceftazidime, tobramycin, levofloxacin, silver, copper, hydroxyapatite, vancomycin, ciprofloxacin, rifampin, mupirocin, RIP, kanamycin, brominated furonone, algae byproducts, bacitracin, oxacillin, nafcillin, floxacillin, clindamycin, cephradin, neomycin, methicillin, oxytetracycline hydrochloride, Selenium. Gene Delivery Genes for nitric oxide synthase, human growth hormone, antisense oligonucleotides Local Tissue Alcohol, H2O, saline, fish oils, vegetable oils, perfusion liposomes Nitric oxide Donor NCX 4016nitric oxide donor derivative of aspirin, Derivatives SNAP Gases Nitric oxide, compound solutions Imaging Agents Halogenated xanthenes, diatrizoate meglumine, diatrizoate sodium Anesthetic Agents Lidocaine, benzocaine Descaling Agents Nitric acid, acetic acid, hypochlorite Anti-Fibrotic Interferon gamma-1b, Interluekin-10 Agents Immunosuppressive/ Cyclosporine, rapamycin, mycophenolate motefil, Immunomodulatory leflunomide, tacrolimus, tranilast, interferon Agents gamma-1b, mizoribine Chemotherapeutic Doxorubicin, paclitaxel, tacrolimus, sirolimus, Agents fludarabine, ranpirnase Tissue Absorption Fish oil, squid oil, omega 3 fatty acids, vegetable Enhancers oils, lipophilic and hydrophilic solutions suitable for enhancing medication tissue absorption, distribution and permeation Anti-Adhesion Hyaluronic acid, human plasma derived surgical Agents sealants, and agents comprised of hyaluronate and carboxymethylcellulose that are combined with dimethylaminopropyl, ehtylcarbodimide, hydrochloride, PLA, PLGA Ribonucleases Ranpirnase Germicides Betadine, iodine, sliver nitrate, furan derivatives, nitrofurazone, benzalkonium chloride, benzoic acid, salicylic acid, hypochlorites, peroxides, thiosulfates, salicylanilide Antiseptics Selenium Analgesics Bupivicaine, naproxen, ibuprofen, acetylsalicylic acid

(38) Some specific examples of therapeutic agents useful in the anti-restenosis realm include cerivastatin, cilostazol, fluvastatin, lovastatin, paclitaxel, pravastatin, rapamycin, a rapamycin carbohydrate derivative (for example, as described in US Patent Application Publication 2004/0235762), a rapamycin derivative (for example, as described in U.S. Pat. No. 6,200,985), everolimus, seco-rapamycin, seco-everolimus, and simvastatin. Depending on the type of therapeutic agent component added to the coating, the resulting coating can be bio-absorbable if the therapeutic agent component is also bio-absorbable. As described in the Summary of the Invention, the present invention relates to coating a medical device such as the stent 10 with a coating such as coating 20. The coating 20 is formed of at least two primary components, namely a bio-absorbable carrier component and a therapeutic agent component. The therapeutic agent component has some form of therapeutic or biological effect. The bio-absorbable carrier component can also have a therapeutic or biological effect. It should again be noted that the bio-absorbable carrier component is different from the conventional bio-degradable substances utilized for similar purposes. The bio-absorbable characteristic of the carrier component enables the cells of body tissue of a patient to absorb the bio-absorbable carrier component itself, rather than breaking down the carrier component into inflammatory by-products and disbursing said by-products of the component for ultimate elimination by the patient's body. Accordingly, anti-inflammatory drug dosages to the patient do not need to be increased to additionally compensate for inflammation caused by the carrier component, as is otherwise required when using polymer-based carriers that themselves cause inflammation.

(39) It should also be noted that the present description makes use of the stent 10 as an example of a medical device that can be coated with the coating 20 of the present invention. However, the present invention is not limited to use with the stent 10. Instead, any number of other implantable medical devices can be coated in accordance with the teachings of the present invention with the described coating 20. Such medical devices include catheters, grafts, balloons, prostheses, stents, other medical device implants, and the like. Implantation refers to both temporarily implantable medical devices, as well as permanently implantable medical devices. In the instance of the example stent 10, a common requirement of stents is that they include some substance or agent that inhibits restenosis. Accordingly, the example coating 20 as described is directed toward the reduction or the elimination of restenosis. However, one of ordinary skill in the art will appreciate that the coating 20 can have other therapeutic or biological benefits. The composition of the coating 20 is simply modified or mixed in a different manner to result in a different biological effect.

(40) FIG. 4 illustrates one method of making the present invention, in the form of the coated stent 10, in accordance with one embodiment of the present invention. The process involves providing a medical device, such as the stent 10 (step 100). A coating, such as coating 20, is then applied to the medical device (step 102). One of ordinary skill in the art will appreciate that this basic method of application of a coating to a medical device such as the stent 10 can have a number of different variations falling within the process described. Depending on the particular application, the stent 10 with the coating 20 applied thereon can be implanted after the coating 20 is applied, or additional steps such as curing, sterilization, and removal of solvent can be applied to further prepare the stent 10 and coating 20. Furthermore, if the coating 20 includes a therapeutic agent that requires some form of activation (such as UV light), such actions can be implemented accordingly.

(41) Furthermore, the step of applying a coating substance to form a coating on the medical device such as the stent 10 can include a number of different application methods. For example, the stent 10 can be dipped into a liquid solution of the coating substance. The coating substance can be sprayed onto the stent 10, which results in application of the coating substance on the exterior surface 18 of the stent 10 as shown in FIG. 3. Another alternative application method is painting the coating substance on to the stent 10, which also results in the coating substance forming the coating 20 on the exterior surface 18 as shown in FIG. 3. One of ordinary skill in the art will appreciate that other methods, such as electrostatic adhesion and other application methods, can be utilized to apply the coating substance to the medical device such as the stent 10. Some application methods may be particular to the coating substance and/or to the structure of the medical device receiving the coating. Accordingly, the present invention is not limited to the specific embodiment described herein, but is intended to apply generally to the application of the coating substance to the medical device, taking whatever precautions are necessary to make the resulting coating maintain desired characteristics.

(42) FIG. 5 is a flowchart illustrating one example implementation of the method of FIG. 4. In accordance with the steps illustrated in FIG. 5, a bio-absorbable carrier component is provided along with a therapeutic agent component (step 110). The provision of the bio-absorbable carrier component and the provision of the therapeutic agent component can occur individually, or in combination, and can occur in any order or simultaneously. The bio-absorbable carrier component is mixed with the therapeutic agent component (or vice versa) to form a coating substance (step 112). The coating substance is applied to the medical device, such as the stent 10, to form the coating (step 114). The coated medical device is then sterilized using any number of different sterilization processes (step 116). For example, sterilization can be implemented utilizing ethylene oxide, gamma radiation, E beam, steam, gas plasma, or vaporized hydrogen peroxide. One of ordinary skill in the art will appreciate that other sterilization processes can also be applied, and that those listed herein are merely examples of sterilization processes that result in a sterilization of the coated stent, preferably without having a detrimental effect on the coating 20.

(43) The formation of the bio-absorbable carrier component and the therapeutic agent component can be done in accordance with different methods. FIG. 6 is a flow chart illustrating one example method for forming each of the components. Vitamin E is mixed with a bio-absorbable carrier to form a bio-absorbable carrier component (step 120). A solvent is mixed with a therapeutic agent to form a therapeutic agent component (step 122). The solvent can be chosen from a number of different alternatives, including ethanol or N-Methyl-2-Pyrrolidone (NMP). The bio-absorbable carrier component is then mixed with the therapeutic agent component to form the coating substance (step 124). The solvent can then be removed with vacuum or heat. It should be noted that the preparation of the bio-absorbable carrier component and the therapeutic agent component can be done in either order, or substantially simultaneously. Additionally, in an alternative approach, the solvent can be omitted altogether.

(44) In accordance with another embodiment of the present invention a surface preparation or pre-treatment 22, as shown in FIG. 8, is provided on a stent 10. More specifically and in reference to the flowchart of FIG. 7, a pre-treatment substance is first provided (step 130). The pre-treatment substance is applied to a medical device, such as the stent 10, to prepare the medical device surface for application of the coating (step 132). If desired, the pre-treatment 22 is cured (step 134). Curing methods can include processes such as application of UV light or application of heat to cure the pre-treatment 22. A coating substance is then applied on top of the pre-treatment 22 (step 136). The coated medical device is then sterilized using any number of sterilization processes as previously mentioned (step 138).

(45) FIG. 8 illustrates the stent 10 having two coatings, specifically, the pre-treatment 22 and the coating 20. The pre-treatment 22 serves as a base or primer for the coating 20. The coating 20 conforms and adheres better to the pre-treatment 22 verses directly to the stent 10, especially if the coating 20 is not heat or UV cured. The pre-treatment can be formed of a number of different materials or substances. In accordance with one example embodiment of the present invention, the pre-treatment is formed of a bio-absorbable substance, such as a naturally occurring oil (e.g., fish oil). The bio-absorbable nature of the pre-treatment 22 results in the pre-treatment 22 ultimately being absorbed by the cells of the body tissue after the coating 20 has been absorbed.

(46) It has been previously mentioned that curing of substances such as fish oil can reduce or eliminate some of the therapeutic benefits of the omega-3 fatty acids, including anti-inflammatory properties and healing properties. However, if the coating 20 contains the bio-absorbable carrier component formed of the oil having the therapeutic benefits, the pre-treatment 22 can be cured to better adhere the pre-treatment 22 to the stent 10, without losing all of the therapeutic benefits resident in the pre-treatment 22, or in the subsequently applied coating 20. Furthermore, the cured pre-treatment 22 provides better adhesion for the coating 20 relative to when the coating 20 is applied directly to the stent 10 surface. In addition, the pre-treatment 22, despite being cured, remains bio-absorbable, like the coating 20.

(47) The pre-treatment 22 can be applied to both the interior surface 16 and the exterior surface 18 of the stent 10, if desired, or to one or the other of the interior surface 16 and the exterior surface 18. Furthermore, the pre-treatment 22 can be applied to only portions of the surfaces 16 and 18, or to the entire surface, if desired.

(48) The application of the coating 20 to the stent 10, or other medical device, can take place in a manufacturing-type facility and subsequently shipped and/or stored for later use. Alternatively, the coating 20 can be applied to the stent 10 just prior to implantation in the patient. The process utilized to prepare the stent 10 will vary according to the particular embodiment desired. In the case of the coating 20 being applied in a manufacturing-type facility, the stent 10 is provided with the coating 20 and subsequently sterilized in accordance with any of the methods provided herein, and/or any equivalents. The stent 10 is then packaged in a sterile environment and shipped or stored for later use. When use of the stent 10 is desired, the stent is removed from the packaging and implanted in accordance with its specific design.

(49) In the instance of the coating being applied just prior to implantation, the stent can be prepared in advance. The stent 10, for example, can be sterilized and packaged in a sterile environment for later use. When use of the stent 10 is desired, the stent 10 is removed from the packaging, and the coating substance is applied to result in the coating 20 resident on the stent 10. The coating 20 can result from application of the coating substance by, for example, the dipping, spraying, brushing, swabbing, wiping, printing, or painting methods.

(50) The present invention provides the coating 20 for medical devices such as the stent 10. The coating is bio-absorbable. The coating 20 includes the bio-absorbable carrier component and can include the therapeutic agent component. The coating 20 of the present invention provides a unique vehicle for the delivery of beneficial substances to the body tissue of a patient.

(51) The bio-absorbable carrier component itself, in the form of fish oil for example, can provide therapeutic benefits in the form of reduced inflammation, and improved healing, if the fish oil composition is not substantially modified during the process that takes the naturally occurring fish oil and forms it into the coating 20. Some prior attempts to use natural oils as coatings have involved mixing the oil with a solvent, or curing the oil in a manner that destroys the beneficial aspects of the oil. The solvent utilized in the coating 20 of the exemplar embodiment of the present invention (NMP) does not have such detrimental effects on the therapeutic properties of the fish oil. Thus the omega-3 fatty acids, and the EPA and DHA substances are substantially preserved in the coating of the present invention. Furthermore, the coating 20 of the present invention is not heat cured or UV light cured to an extent that would destroy all or a substantial amount of the therapeutic benefits of the fish oil, unlike some prior art attempts.

(52) Therefore, the coating 20 of the present invention includes the bio-absorbable carrier component in the form of the naturally occurring oil (i.e., fish oil, or any equivalents). The bio-absorbable carrier component is thus able to be absorbed by the cells of the body tissue. More specifically, there is a phospholipid layer in each cell of the body tissue. The fish oil, and equivalent oils, contain lipids as well. There is a lipophilic action that results where the lipids are attracted by each other in an effort to escape the aqueous environment surrounding the lipids. Accordingly the lipids attract, the fish oil fatty acids bind to the cells of the tissue, and subsequently alter cell membrane fluidity and cellular uptake. If there is a therapeutic agent component mixed with the bio-absorbable carrier component, the therapeutic component associated with the fish oil lipids penetrates the cells in an altered manner.

(53) As previously mentioned, prior attempts to create drug delivery platforms such as coatings on stents primarily make use of polymer based coatings to provide the ability to better control the release of the therapeutic agent. Essentially, the polymer in the coating releases the drug or agent at a predetermined rate once implanted at a location within the patient. Regardless of how much of the therapeutic agent would be most beneficial to the damaged tissue, the polymer releases the therapeutic agent based on properties of the polymer coating. Accordingly, the effect of the coating is substantially local at the surface of the tissue making contact with the coating and the stent. In some instances the effect of the coating is further localized to the specific locations of stent struts pressed against the tissue location being treated. These prior approaches can create the potential for a localized toxic effect.

(54) Contrarily with the present invention, because of the lipophilic mechanism enabled by the bio-absorbable lipid based coating 20 formed using a cross-linked gel derived from at least one fatty acid compound in accordance with the present invention, the uptake of the therapeutic agent is facilitated by the delivery of the therapeutic agent to the cell membrane by the bio-absorbable carrier component. Further, the therapeutic agent is not freely released into the body fluids, but rather, is delivered directly to the cells and tissue. In prior configurations using polymer based coatings, the drugs were released at a rate regardless of the reaction or need for the drug on the part of the cells receiving the drug.

(55) In addition, the bio-absorbable nature of the carrier component and the resulting coating (in the instances where a bio-absorbable therapeutic agent component is utilized) results in the coating 20 being completely absorbed over time by the cells of the body tissue. There is no break down of the coating into sub parts and substances which induce an inflammatory response that are eventually distributed throughout the body and in some instances disposed of by the body, as is the case with biodegradable coatings. The bio-absorbable nature of the coating 20 of the present invention results in the coating being absorbed, leaving only the stent structure, or other medical device structure. There is no foreign body inflammatory response to the bio-absorbable carrier component.

(56) Despite action by the cells, the coating 20 of the present invention is further configured to release the therapeutic agent component at a rate no faster than a selected controlled release rate over a period of weeks to months. The controlled release rate action is achieved by providing an increased level of vitamin E in the mixture with the fish oil, to create a more viscous, sticky, coating substance that better adheres and lasts for a longer duration on the implanted medical device. The controlled release rate can include an initial burst of release, followed by the sustained multi-week to multi-month period of release. Correspondingly, with a greater amount of fatty acids relative to the level of vitamin E, the controlled release rate can be increased. The fatty acids can be found in the oil, and/or fatty acids such as myristic acid can be added to the oil. Thus, the ratio of fatty acids to alpha-tocopherol can be varied in the preparation of the coating 20 to vary the subsequent release rate of the therapeutic agent in a controlled and predictable manner.

(57) In addition, the oil provides a lubricious surface against the vessel walls. As the stent 10 having the coating 20 applied thereon is implanted within a blood vessel, for example, there can be some friction between the stent walls and the vessel walls. This can be injurious to the vessel walls, and increase injury at the diseased vessel location. The use of the naturally occurring oil, such as fish oil, provides extra lubrication to the surface of the stent 10, which reduces the initial injury. With less injury caused by the stent, there is less of an inflammatory response, and less healing required.

(58) Several example implementations have been carried out to demonstrate the effectiveness of the coating 20 of the present invention. Details concerning the example implementations follow.

EXAMPLE #1

(59) A bio-absorbable carrier component was made by mixing 70% vitamin E and 30% EPAX 3000 TG Fish Oil. Cilostazol was mixed with NMP at a loading of 2.5% by weight to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a ratio of 1:1 with the therapeutic agent component to form a coating substance. The coating substance was applied to a stent and dried in a vacuum chamber for 15 minutes. The stent with the coating was then placed in phosphate buffered saline (PBS) for dissolution to measure the delivery of the Cilostazol drug.

EXAMPLE #2

(60) A bio-absorbable carrier component was made by mixing 30% vitamin E and 70% EPAX 3000 TG Fish Oil. Cilostazol was mixed with NMP at a loading of 2.5% by weight to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a ratio of 1:1 with the therapeutic agent component to form a coating substance. The coating substance was applied to a stent and dried in a vacuum chamber for 15 minutes. The stent with the coating was then placed in phosphate buffered saline (PBS) for dissolution to measure the delivery of the Cilostazol drug.

EXAMPLE #3

(61) A bio-absorbable carrier component was made by mixing 30% vitamin E and 70% EPAX 3000 TG Fish Oil. Cilostazol was mixed with NMP at a loading of 2.5% by weight to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a ratio of 1:1 with the therapeutic agent component to form a coating substance. The coating substance was applied to a stent and dried in a vacuum chamber for 15 minutes. The stent was placed in an oven for 5 days at 150 F. The stent with the coating was then placed in phosphate buffered saline (PBS) for dissolution to measure the delivery of the Cilostazol drug.

EXAMPLE #4

(62) A bio-absorbable carrier component was made by mixing 30% vitamin E and 70% EPAX 3000 TG Fish Oil. Cilostazol was mixed with NMP at a loading of 2.5% by weight to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a ratio of 1:1 with the therapeutic agent component to form a coating substance. The coating substance was applied to a stent and dried in a vacuum chamber for 15 minutes. The stent was placed under UV light for 5 days. The stent with the coating was then placed in phosphate buffered saline (PBS) for dissolution to measure the delivery of the Cilostazol drug.

EXAMPLE #5

(63) A bio-absorbable carrier component was made by mixing 30% vitamin E and 70% EPAX 3000 TG Fish Oil. Cilostazol was mixed with NMP at a loading of 2.5% by weight to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a ratio of 1:1 with the therapeutic agent component to form a coating substance. The coating substance was applied to a stent and dried in a vacuum chamber for 15 minutes. The stent was sent for one cycle of EtO sterilization. The stent with the coating was then placed in phosphate buffered saline (PBS) for dissolution to measure the delivery of the Cilostazol drug.

EXAMPLE #6

(64) A bio-absorbable carrier component was made by mixing 30% vitamin E and 70% Lorodan Fish Oil Fatty Acids. Cilostazol was mixed with NMP at a loading of 2.5% by weight to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a ratio of 1:1 with the therapeutic agent component to form a coating substance. The coating substance was applied to a stent and dried in a vacuum chamber for 15 minutes. The stent with the coating was then placed in phosphate buffered saline (PBS) for dissolution to measure the delivery of the Cilostazol drug.

EXAMPLE #7

(65) A bio-absorbable carrier component was made by mixing 30% vitamin E and 70% Lorodan Fish Oil Fatty Acids. Cilostazol was mixed with NMP at a loading of 2.5% by weight to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a ratio of 1:1 with the therapeutic agent component to form a coating substance. The coating substance was applied to a stent and dried in a vacuum chamber for 15 minutes. The stent was placed in an oven for 5 days at 150 F. The stent with the coating was then placed in phosphate buffered saline (PBS) for dissolution to measure the delivery of the Cilostazol drug.

EXAMPLE #8

(66) A bio-absorbable carrier component was made by mixing 15% vitamin E, 35% EPAX 3000 TG Fish Oil, and 50% Myristic Acid. Cilostazol was mixed with NMP at a loading of 2.5% by weight to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a ratio of 1:1 with the therapeutic agent component to form a coating substance. The coating substance was applied to a stent and dried in a vacuum chamber for 15 minutes. The stent with the coating was then placed in phosphate buffered saline (PBS) for dissolution to measure the delivery of the Cilostazol drug.

EXAMPLE #9

(67) A bio-absorbable carrier component was made by mixing 30% vitamin E, 66.5% EPAX 3000 TG Fish Oil, and 3.5% Linseed Oil. Cilostazol was mixed with NMP at a loading of 2.5% by weight to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a ratio of 1:1 with the therapeutic agent component to form a coating substance. The coating substance was applied to a stent and dried in a vacuum chamber for 15 minutes. The stent was placed in an oven for 5 days at 150 F. The stent with the coating was then placed in phosphate buffered saline (PBS) for dissolution to measure the delivery of the Cilostazol drug.

(68) The results of the above different example implementations measured over a time period of 5 days showed a range of release rates of the Cilostazol drug between about 20 to 65 micrograms at about 1 day to about 25 to 85 micrograms at about 5 days. In other example implementations using Rapamycin with similar formulations, Rapamycin was found present in the vessel tissue after 28 days.

(69) In an additional example implementation, a stent was coated with a primer or pre-treatment of fish oil prior to the application of the drug loaded coating. The details are provided below.

EXAMPLE #10

(70) A stainless steel stent was crimped onto a balloon then coated with EPAX 3000 TG Fish Oil that was heated at 250 F. for approximately 72 hours. This heating action increased the viscosity of the oil to honey-like consistency. The stent was then dipped into a solution of fish oil mixed with vitamin E and solvent. The stent was placed under vacuum pressure to remove the solvent. Subsequent analysis demonstrated that 10 out of 10 sampled areas of the stent maintained a detectable (>m) amount of coating present on the stent, substantially evenly distributed.

EXAMPLE #11 (Control Coating)

(71) A bio-absorbable carrier component was made by mixing 50% vitamin E and 50% EPAX 3000 TG Fish Oil. The bio-absorbable carrier component was mixed at a weight ratio of 1:1 with 1-methyl-2-pyrrolidone (NMP) to formulate a coating substance [Formulation A]. The stent/balloon section of an Atrium Flyer coronary stent system was cleaned prior to coating by dipping it into a sodium bicarbonate solution followed by sonication in ultrapure HPLC grade water for five minutes. The wet stent/balloon was removed from the water and dried using flowing hot air for 2 minutes. The cleaned stent/balloon was immersion dip coated in Formulation A, then removed and exposed to flowing hot air for 30 seconds. The entire stent/catheter assembly was then placed in a vacuum chamber for 15 minutes at a pressure of approximately 50 mTorr. The assembly was removed from the vacuum chamber, a protector sheath was placed over the coated stent/balloon section and the entire stent/catheter assembly was returned to its original hoop package insert, then placed in a Tyvek pouch, sealed and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the packaged assembly was vacuum sealed in a foil pouch.

(72) A representative coated stent was placed in an appropriate dissolution medium as a control sample when determining drug release in the following samples.

EXAMPLE #12 (High Dose Rapamycin (200 ug/Stent))

(73) A bio-absorbable carrier component was made by mixing 50% vitamin E and 50% EPAX 3000 TG Fish Oil. Rapamycin was mixed with 1-Methyl-2-Pyrrolidone (NMP) solvent at a loading of 350 mg/ml to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a weight ratio of 0.5:1 with the therapeutic agent component to formulate a coating substance [Formulation B]. The stent/balloon section of an Atrium Flyer coronary stent system was cleaned prior to coating by dipping it into a sodium bicarbonate solution followed by sonication in ultrapure HPLC grade water for five minutes. The wet stent/balloon was then removed from the water and dried using flowing hot air for 2 minutes. The cleaned stent/balloon was then immersion dip coated in Formulation B, then removed and exposed to flowing hot air for 30 seconds. The entire stent/catheter assembly was then placed in a vacuum chamber for 15 minutes at a pressure of approximately 50 mTorr. The assembly was removed from the vacuum chamber, a protector sheath was placed over the coated stent/balloon section and the entire stent/catheter assembly was returned to its original hoop package insert, then placed in a Tyvek pouch, sealed and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the packaged assembly was vacuum sealed in a foil pouch.

(74) The calculated amount of drug on a 3.016 mm stent with this formulation was 200 ug. A representative coated stent sample was then placed in Phosphate Buffered saline (PBS) for dissolution to measure the rapamycin release over time.

EXAMPLE #13 (Low Dose Rapamycin (50 ug/Stent))

(75) A bio-absorbable carrier component was made by mixing 50% vitamin E and 50% EPAX 3000 TG Fish Oil. Rapamycin was mixed with 1-Methyl-2-Pyrrolidone (NMP) solvent at a loading of 85 mg/ml to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a weight ratio of 0.84:1 with the therapeutic agent component to formulate a coating substance [Formulation C].

(76) The stent/balloon section of an Atrium Flyer coronary stent/catheter system was cleaned prior to coating by dipping the stent into a sodium bicarbonate solution followed by sonication in ultrapure HPLC grade water for five minutes. The wet stent/balloon was removed from the water and dried using flowing hot air for 2 minutes. The cleaned stent/balloon was immersion dip coated in Formulation C, and then exposed to flowing hot air for 30 seconds. The entire stent/catheter assembly was then placed in a vacuum chamber for 15 minutes at a pressure of approximately 50 mTorr. The assembly was removed from the vacuum chamber, and a protector sheath was placed over the coated stent/balloon section. The entire stent/catheter assembly was returned to its original hoop package insert, then placed in a Tyvek pouch, sealed and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the packaged assembly was vacuum sealed in a foil pouch.

(77) The calculated amount of drug on a 3.016 mm stent with this formulation was 50 ug. A representative coated stent sample was then placed in Phosphate Buffered saline (PBS) for dissolution to measure rapamycin release over time.

EXAMPLE #14 (Preparation and Application of Primer)

(78) Primer is prepared by heating or UV treating the oil to increase the viscosity. Primer coated stents were prepared for subsequent drug coating as follows. The stent/balloon section of an Atrium Flyer coronary stent/catheter system was cleaned prior to primer application by dipping into sodium bicarbonate solution followed by sonication in ultrapure HPLC grade water for five minutes. The stent/balloon was removed from the water and dried using flowing hot air for 2 minutes. EPAX 3000TG fish oil was placed in an oven at 250 F. until the viscosity was of the desired consistency, approximately 30 hours. A thin layer of the primer was applied evenly around the surface of the pre-crimped stent/balloon, using an applicator. The primer coated stent/balloon was subsequently coated with the appropriate formulation, as necessary.

EXAMPLE #15 Hot Cilostazol (105 ug/Stent)

(79) A bio-absorbable carrier component was made by mixing 70% vitamin E and 30% EPAX 3000 TG fish oil. Separately, 100 mg of Cilostazol was mixed with 0.5 ml of NMP (200 mg/ml concentration). Both the drug-solvent mixture and the bio-absorbable carrier component were heated to 150 F. for approximately 10 minutes. Once both mixtures reached temperature, they were combined at a weight ratio of 1:1, gently mixed, and again heated to 150 F. for approximately 5 minutes, until the mixture equilibrated at 150 F., to formulate a coating substance [Formulation D].

(80) A primer coated Atrium Flyer stent/balloon was prepared as described in Example #14, and immersion dip coated in Formulation D. The entire stent/catheter assembly was then placed in a vacuum chamber for a period of 4 hours at a pressure of approximately 50 mTorr. The assembly was removed from the vacuum chamber, a protector sheath was placed over the coated stent/balloon section and the entire stent/catheter assembly was returned to its original hoop package insert, then placed in a Tyvek pouch, sealed and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the packaged assembly was vacuum sealed in a foil pouch.

(81) The calculated amount of drug on a 3.016 mm stent with this formulation was 105 ug. A representative coated stent sample was then placed in water for dissolution to measure release of Cilostazol drug over time.

(82) When viewed under 20 magnification it was evident that there were substantially fewer crystals present than there were in a similar formulation that was prepared at room temperature.

EXAMPLE #16 Cilostazol High Solids (388 ug/Stent)

(83) A bio-absorbable carrier component was made by mixing 30% vitamin E and 70% EPAX 3000 TG Fish Oil. The bio-absorbable carrier component was mixed with cilostazol powder at a drug loading of 36% to formulate a coating substance [Formulation E].

(84) The stent/balloon section of an Atrium Flyer coronary stent system was sonicated in ultrapure HPLC grade water for five minutes. The stent/balloon was removed from the water and dried using flowing hot air for 2 minutes. The cleaned stent/balloon was then coated with Formulation E using an applicator. A protector sheath was then placed over the coated stent/balloon section and the entire stent/catheter assembly was returned to its original hoop package insert, placed in a Tyvek pouch, sealed and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the packaged assembly was vacuum sealed in a foil pouch.

(85) The calculated amount of drug on a 3.016 mm stent with this formulation was 388 ug. A representative coated stent sample was then placed in water for dissolution to measure release of the Cilostazol drug over time.

EXAMPLE #17 Methylprednisolone High Solids (440 ug/Stent)

(86) A bio-absorbable carrier component was made by mixing 30% vitamin E and 70% EPAX 3000 TG Fish Oil. The bio-absorbable carrier component was mixed with methylprednisolone powder at a drug loading of 40% to formulate a coating substance [Formulation F].

(87) The stent/balloon section of an Atrium Flyer coronary stent system was cleaned prior to coating by sonication in ultrapure HPLC grade water for five minutes. The wet stent/balloon was then removed from the water and dried using flowing hot air for 2 minutes. The cleaned stent/balloon was coated with Formulation F using an applicator. A protector sheath was then placed over the coated stent/balloon section and the entire catheter assembly was returned to its original hoop package insert, placed in a Tyvek pouch, sealed and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the sample was vacuum sealed in a foil pouch.

(88) The calculated amount of drug on a 3.016 mm stent with this formulation was approximately 550-700 ug. A representative coated stent sample was then placed in water for dissolution to measure release of the methylprednisolone drug over time. The amount of methylprednisone released over time in water from the coated stent is depicted in FIG. 9.

EXAMPLE #18 High Dose Methylprednisolone

(89) A bio-absorbable carrier component was made by mixing 30% vitamin E and 70% EPAX 3000 TG Fish Oil. Methylprednisolone was mixed with NMP at a loading of 406 mg/ml to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a weight ratio of 0.37:1 with the therapeutic agent component to formulate a coating substance [Formulation G].

(90) The stent/balloon section of an Atrium Flyer coronary stent system was prepared and primed as described in Example #14. The primer coated stent/balloon was then immersion dip coated in Formulation G. The entire assembly was then placed in a vacuum chamber for 4 hours at a pressure of approximately 50 mTorr. The assembly was removed from the vacuum chamber, a protector sheath was placed over the coated stent/balloon section and the entire assembly was returned to its original hoop package insert, then placed in a sealed Tyvek pouch and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the sample was vacuum sealed in a foil pouch. The calculated amount of drug on a 3.016 mm stent with this formulation was 259 ug. A representative coated stent sample was then placed in water for dissolution to measure the release of the methylprednisolone drug over time. The amount of methylprednisone released over time in water from the coated stent is depicted in FIG. 10.

EXAMPLE #19 Low Dose Cilostazol (30 ug/Stent)

(91) A bio-absorbable carrier component was made by mixing 70% vitamin E and 30% EPAX 3000 TG Fish Oil. Cilostazol was mixed with NMP at a loading of 52 mg/ml to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a weight ratio of 0.9:1 with the therapeutic agent component to formulate a coating substance [Formulation H].

(92) The stent/balloon section of an Atrium Flyer coronary stent system was prepared and primed as described in Example #14. The primer coated stent/balloon was then immersion dip coated in Formulation H. The entire stent/catheter assembly was then placed in a vacuum chamber for 4 hours at a pressure of approximately 50 mTorr. The assembly was removed from the vacuum chamber, a protector sheath was placed over the coated stent/balloon section and the entire assembly was returned to its original hoop package insert, then placed in a Tyvek pouch, sealed and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the sample was vacuum sealed in a foil pouch.

(93) The calculated amount of drug on a 3.016 mm stent with this formulation was 30 ug. A representative coated stent sample was then placed in water for dissolution to measure the release of the Cilostazol drug over time. The cumulative amount of cilostazol released over time in water from the coated stent is depicted in FIG. 11.

EXAMPLE #20 Low Dose Methylprednisolone (30 ug/Stent)

(94) A bio-absorbable carrier component was made by mixing 70% vitamin E and 30% EPAX 3000 TG Fish Oil. Methylprednisolone was mixed with NMP at a loading of 56 mg/ml to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a weight ratio of 0.9:1 with the therapeutic agent component to formulate a coating substance [Formulation I].

(95) The stent/balloon section of an Atrium Flyer coronary stent system was prepared and primed as described in Example #14. The primer coated stent/balloon was then immersion dip coated in Formulation I. The entire stent/catheter assembly was then placed in a vacuum chamber for 4 hours at a pressure of approximately 50 mTorr. The assembly was removed from the vacuum chamber, a protector sheath was placed over the coated stent/balloon section and the entire assembly was returned to its original hoop package insert, then placed in a Tyvek pouch, sealed and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the sample was vacuum sealed in a foil pouch.

(96) The calculated amount of drug on a 3.016 mm stent with this formulation was 30 ug. A representative coated stent sample was then placed in water for dissolution to measure release of the methylprednisolone drug over time.

EXAMPLE #21 Paclitaxel High Solids (106 ug/Stent)

(97) A bio-absorbable carrier component was made by mixing 30% vitamin E and 70% EPAX 3000 TG Fish Oil. The bio-absorbable carrier component was mixed with paclitaxel powder at a drug loading of 11% to formulate a coating substance [Formulation J].

(98) The stent/balloon section of an Atrium Flyer coronary stent system was cleaned prior to coating by sonication in ultrapure HPLC grade water for five minutes. The wet stent/balloon was then removed from the water and dried using flowing hot air for 2 minutes. The cleaned stent/balloon was then coated with Formulation J using an applicator. A protector sheath was then placed over the coated stent/balloon section and the entire assembly was returned to its original hoop package insert, placed in a sealed Tyvek pouch and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the sample was vacuum sealed in a foil pouch.

(99) The calculated amount of drug on a 3.016 mm stent with this formulation was 106 ug. A representative coated stent sample was then placed in 35% Acetonitrile/water for dissolution to measure release of the paclitaxel drug over time. The amount of paclitaxel released over time in a 35% solution of acetonitrile/water from the coated stent is depicted in FIG. 12.

EXAMPLE #22 Medium Dose Paclitaxel (30 ug/Stent)

(100) A bio-absorbable carrier component was made by mixing 70% vitamin E and 30% EPAX 3000 TG Fish Oil. Paclitaxel was mixed with Ethanol at a loading of 40 mg/ml to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a weight ratio of 0.94:1 with the therapeutic agent component to formulate a coating substance [Formulation K].

(101) The stent/balloon section of an Atrium Flyer coronary stent system was prepared and primed as described in Example #14. The primer coated stent/balloon was then immersion dip coated in Formulation K. The entire assembly was then placed in a vacuum chamber for 4 hours at a pressure of approximately 50 mTorr. The assembly was removed from the vacuum chamber, a protector sheath was placed over the coated stent/balloon section and the entire assembly was returned to its original hoop package insert, then placed in a sealed Tyvek pouch and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the sample was vacuum sealed in a foil pouch.

(102) The calculated amount of drug on a 3.016 mm stent with this formulation was 30 ug. A representative coated stent sample was then placed in 35% Acetonitrile/water for dissolution to measure release of the paclitaxel drug over time.

EXAMPLE #23 Low Dose Paclitaxel (5 ug/Stent)

(103) A bio-absorbable carrier component was made by mixing 70% vitamin E and 30% EPAX 3000 TG Fish Oil. Paclitaxel was mixed with Ethanol at a loading of 8 mg/ml to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a weight ratio of 1:1 with the therapeutic agent component to formulate a coating substance [Formulation L].

(104) The stent/balloon section of an Atrium Flyer coronary stent system was prepared and primed as described in Example #14. The primer coated stent/balloon was then immersion dip coated in Formulation L. The entire assembly was then placed in a vacuum chamber for 4 hours at a pressure of approximately 50 mTorr. The assembly was removed from the vacuum chamber, a protector sheath was placed over the coated stent/balloon section and the entire assembly was returned to its original hoop package insert, then placed in a sealed Tyvek pouch and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the sample was vacuum sealed in a foil pouch.

(105) The calculated amount of drug on a 3.016 mm stent with this formulation was 5 ug. A representative coated stent sample was then placed in 35% Acetonitrile/water for dissolution to measure release of the paclitaxel drug over time.

EXAMPLE #24 High Dose Rapamycin (200 ug/Stent)

(106) A bio-absorbable carrier component was made by mixing 50% vitamin E and 50% EPAX 3000 TG Fish Oil. Rapamycin was mixed with NMP at a loading of 350 mg/ml to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a weight ratio of 0.5:1 with the therapeutic agent component to formulate a coating substance [Formulation M].

(107) The stent/balloon section of an Atrium Flyer coronary stent system was cleaned prior to coating by sonication in ultrapure HPLC grade water for five minutes. The wet stent/balloon was then removed from the water and dried using a flowing hot air for 2 minutes. The cleaned stent/balloon was then immersion dip coated in Formulation M then exposed to flowing hot air. The entire assembly was then placed in a vacuum chamber for 4 hours at a pressure of approximately 50 mTorr. The assembly was removed from the vacuum chamber, a protector sleeve was placed over the stent/balloon section and the entire assembly was returned to its original hoop package insert, then placed in a Tyvek pouch, sealed and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the sample was vacuum sealed in a foil pouch.

(108) The calculated amount of drug on a 3.016 mm stent with this formulation was 200 ug. A representative coated stent sample was then placed in Phosphate Buffered saline (PBS) for dissolution to measure release of the rapamycin drug over time.

EXAMPLE #25 Pre-Dried Paclitaxel Formulation

(109) A bio-absorbable carrier component was made by mixing 70% vitamin E and 30% EPAX 3000 TG Fish Oil, as prepared in Example #14. Paclitaxel was mixed with Ethanol at a loading of 39 mg/ml to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a weight ratio of 0.9:1 with the therapeutic agent component to formulate a coating mixture. The coating mixture was then placed in a vacuum chamber at a pressure of approximately 50 mTorr for a period of 16 hours to formulate a coating substance [Formulation N].

(110) The coating substance was highly viscous and free from crystal formation. The stent/balloon section of an Atrium Flyer coronary stent system was then cleaned prior to coating by sonication in ultrapure HPLC grade water for five minutes. The wet stent/balloon section was then removed from the water and dried using a flowing hot air for 2 minutes. The cleaned stent/balloon was then coated with the Formulation N using an applicator. A protector sheath was then placed over the coated stent/balloon section and the entire assembly was returned to its original hoop package insert, placed in a sealed Tyvek pouch and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the sample was vacuum sealed in a foil pouch.

(111) The calculated amount of drug on a 3.016 mm stent with this formulation was 50 ug. A representative coated stent sample was then placed in 35% acetonitrile/water for dissolution to measure release of the Paclitaxel drug over time.

EXAMPLE #26 Pre Dried Cilostazol Formulation

(112) A bio-absorbable carrier component was made by mixing 70% vitamin E and 30% EPAX 3000 TG Fish Oil, as prepared in Example #14. Cilostazol was mixed with NMP at a loading of 24 mg/ml to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a weight ratio of 0.86:1 with the therapeutic agent component to form a coating mixture. The coating mixture was then placed in a vacuum chamber at a pressure of approximately 50 mTorr for a period of 16 hours to formulate a coating substance [Formulation O].

(113) A highly viscous coating substance that was free of crystals was obtained. The stent/balloon section of an Atrium Flyer coronary stent system was then cleaned prior to coating by sonication in ultrapure HPLC grade water for five minutes. The wet stent/balloon section was then removed from the water and dried using flowing hot air for 2 minutes. The cleaned stent/balloon was then coated with Formulation O using an applicator. A protector sheath was then placed over the coated stent/balloon section and the entire assembly was returned to its original hoop package insert, placed in a sealed Tyvek pouch and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the sample was vacuum sealed in a foil pouch.

(114) A representative coated stent sample was then placed in phosphate buffered saline solution (PBS) for dissolution to measure release of the Cilostazol drug over time.

EXAMPLE #27 Pre Dried Rapamycin Formulation

(115) A bio-absorbable carrier component was made by mixing 70% vitamin E and 30% EPAX 3000 TG Fish Oil. Rapamycin was mixed with NMP at a loading of 97 mg/ml to form a therapeutic agent component. The bio-absorbable carrier component was mixed at a weight ratio of 0.77:1 with the therapeutic agent component to form a coating mixture. The coating mixture was then placed in a vacuum chamber at a pressure of approximately 50 mTorr for a period of 16 hours to formulate a coating substance [Formulation P].

(116) The coating mixture was highly viscous and free from crystal formation. The stent/balloon section of an Atrium Flyer coronary stent system was then cleaned prior to coating by sonication in ultrapure HPLC grade water for five minutes. The wet stent/balloon section was then removed from the water and dried using flowing hot air for 2 minutes. The cleaned stent/balloon was then coated with the Formulation P using an applicator. A protector sheath was then placed over the coated stent/balloon section and the entire assembly was returned to its original hoop package insert, placed in a sealed Tyvek pouch and sterilized using Vaporized Hydrogen Peroxide (VHP). After sterilization the sample was vacuum sealed in a foil pouch.

(117) A representative coated stent sample was then placed in phosphate buffered saline solution (PBS) for dissolution to measure release of the Rapamycin drug over time.

EXAMPLE #28 Animal Study

(118) Several different stent and coating combinations were created and implanted into rabbit iliac arteries for 28 days and then histopathology (a measure of biological response to an implant at the cellular level) and histomorphometry (a measure of the neointimal thickness and lumen area of the stented vessel) were performed. A bare stent (stent A), a stent having a non-polymer coating of the present invention (stent B), and a stent having a non-polymer coating including a drug (Rapamycin) (stent C) were the three stent and coating combinations using an Atrium Medical Corporation Flyer stainless steel stent that were implanted. A polymer coated stent with drug (Rapamycin) made by Johnson & Johnson (Cypher stent) (stent D) was a fourth stent combination implanted.

EXAMPLE #29 Release Rate Comparison

(119) Three coatings in accordance with the present invention were applied to the stents having coatings, and the release rates compared. The results are shown in FIG. 13.

(120) Referring to FIG. 13, the top diamond line on the curve that is labeled [high dose] is a 30.1% Rapamycin formulation made with 50% vitamin E and 50% fish oil. The drug was dissolved in the solvent (NMP) first and then combined with the fish oil/vitamin E mixture and vortexed. The solvent was then removed with vacuum. The formulation was dip coated on stents and then dried over night in a bell jar. The stent was then expanded and submitted for release testing.

(121) The next line on the graph that is labeled [low dose] is a sample containing 18.49% rapamycin in a coating that is 30% Vitamin E and 70% fish oil. The coating was made using NMP as the solvent. The solvent was then removed with vacuum. The stent was then expanded and submitted for release testing.

(122) The next line on the graph that is labeled Cypher stent was a Cypher stent, measuring 2.518 mm. Drug release was measured from an expanded stent.

(123) The final line on the graph that is labeled [high dose]XR was a 19.18% Rapamycin insoluble formulation that was made in 30% vitamin E and 70% thickened fish oil. This sample had no solvent and was applied using a stent protector. The sample was then expanded and submitted for release testing.

(124) For purposes of the analysis, the Stents are put into 4 ml vials along with 4 ml of PBS on the incubated (37 C.) shaker table and samples are taken at appropriate time points for measuring drug concentration/release using HPLC. When the stent was ready to be sampled the stent was removed from the vial and put in a new vial with a fresh 4 mls of PBS and returned to the incubated shaker. The sample was prepared for HPLC by adding 600 ul of the PBS from the test sample to 3400 ul of Methanol to obtain an 85:15 ratio. The sample was then mixed using the vortexer. This methanol diluted sample was then injected onto the HPLC and drug release was calculated.

(125) The stents loaded with the bio-absorbable coating of the present invention and low (50 g) amounts of Rapamycin (labeled [low dose] stent) and the stents loaded with the bio-absorbable coating of the present invention and high (200 g) amounts of Rapamycin (labeled [high dose] stent) implanted in the iliac arteries were well tolerated and produced no adverse reactions.

(126) The stents having the bio-absorbable coating of the present invention and loaded with Rapamycin significantly reduced neointimal growth, and experienced delayed healing, but the stents were well endothelialized after 28 days. The stents having the bio-absorbable coating of the present invention and the stents having the bio-absorbable coating of the present invention with drug caused relatively less arterial injury relative to the Cypher stent (labeled Cypher stent), which caused more than twice the amount of arterial injury. The Cypher stent produced the greatest reduction in neointimal growth, however also had the greatest delay in healing, which was represented by fibrin deposition and poor endothelialization relative to the other implanted stents. The Cypher stent also experience relatively greater numbers of inflammatory and giant cells relative to the other implanted stents. The Cypher stents experienced at least three times greater amounts of giant cell reaction and the majority of Cypher stent struts showed presence of eosinophils, which were rarely present on the other implanted stents.

(127) Numerous modifications and alternative embodiments of the present invention will be apparent to those skilled in the art in view of the foregoing description. Accordingly, this description is to be construed as illustrative only and is for the purpose of teaching those skilled in the art the best mode for carrying out the present invention. Details of the structure may vary substantially without departing from the spirit of the invention, and exclusive use of all modifications that come within the scope of the appended claims is reserved. It is intended that the present invention be limited only to the extent required by the appended claims and the applicable rules of law.