BIOERODIBLE ENDOPROSTHESIS WITH BIOSTABLE INORGANIC LAYERS

[0001] This application claims priority under 35 USC §119(e) to U.S. Provisional Patent Application Ser. No. 60/845,135, filed on Sep. 15, 2006, the entire contents of which are hereby incorporated by reference.

[0002] TECHNICAL FIELD

[0003] This invention relates to medical devices, such as endoprostheses, and methods of making and using the same.

[0004] The body includes various passageways including blood vessels such as arteries, and other body lumens. These passageways sometimes become occluded or weakened. For example, they can be occluded by a tumor, restricted by plaque, or weakened by an aneurysm. When this occurs, the passageway can be reopened or reinforced, or even replaced, with a medical endoprosthesis. An endoprosthesis is an artificial implant that is typically placed in a passageway or lumen in the body. Many endoprostheses are tubular members, examples of which include stents, stent-grafts, and covered stents.

[0005] Many endoprostheses can be delivered inside the body by a catheter. Typically the catheter supports a reduced-size or compacted form of the endoprosthesis as it is transported to a desired site in the body, for example the site of weakening or occlusion in a body lumen. Upon reaching the desired site the endoprosthesis is installed so that it can contact the walls of the lumen.

[0006] One method of installation involves expanding the endoprosthesis. The expansion mechanism used to install the endoprosthesis may include forcing it to expand radially. For example, the expansion can be achieved with a catheter that carries a balloon in conjunction with a balloon-expandable endoprosthesis reduced in size relative to its final form in the body. The balloon is inflated to deform and/or expand the endoprosthesis in order to fix it at a predetermined position in contact with the lumen wall. The balloon can then be deflated, and the catheter withdrawn.

[0007] When the endoprosthesis is advanced through the body, its progress can be monitored, e.g., tracked, so that the endoprosthesis can be delivered properly to a target site. After the endoprosthesis is delivered to the target site, the endoprosthesis can be monitored to determine whether it has been placed properly and/or is functioning properly. Methods of tracking and monitoring a medical device include X-ray fluoroscopy and magnetic resonance imaging (MRI).

[0008] In one aspect, the invention features an endoprosthesis, e.g., a stent, having a biostable layer and a bioerodible underlying structure, wherein the biostable layer is about 5% or less of the wall thickness.

[0009] In another aspect, the invention features a method of making an endoprosthesis, e.g., stent, having a biostable layer and an underlying structure.

[0010] In yet another aspect, the invention features a method that includes implanting an endoprosthesis, e.g., stent, having a biostable layer and an underlying structure in a body passageway to stimulate the attachment of endothelial cells to the stent or control the erosion rate of the underlying structure.

[0011] Embodiments may include one or more of the following features. The biostable layer of the endoprosthesis, e.g., stent, has one or more of the following characteristics: a thickness on average of about 10 to 20 nm; an average volume in the range of about 5,000 to 20,000 cubic micrometer per square millimeter of stent surface area; includes ceramic material; includes one or more metal oxides; includes one or more of titanium oxide, ruthenium oxide, or iridium oxide; includes a crystalline form of titanium oxide; includes a plurality of nodules about 15-20 nm in size; is on a surface of the stent, e.g., an interior surface, an exterior surface or a sidewall, of the stent; is covered, in full or in part, by a bioerodible layer; and/or is a monolayer. In embodiments, the bioerodible underlying structure includes one or more bioerodible materials chosen from one or more of a bioerodible metal, a bioerodible metal alloy or a bioerodible non-metal.

[0012] In embodiments, the endoprosthesis, e.g., stent, includes: one or more monolayers of a metal oxide, an organic material, a polymeric material or a biological material; and/or further includes at least one therapeutic agent, e.g., paclitaxel.

[0013] Further embodiments may include one or more of the following features. The biostable layer is formed by a sol-gel process. In embodiments, the process of making the biostable layer includes: modifying a selected portion of the surface of the underlying structure with hydroxyl groups; allowing the hydroxyl groups to react with one or more metal alkoxides to form a covalently-bound biostable layer of the one or more metal alkoxides; (optionally) removing excess adsorbed metal alkoxide; and hydrolyzing the covalently-bound surface of the biostable layer. In embodiments, the process of making endoprosthesis, e.g., stent, having a biostable layer and a bioerodible structure includes: applying the biostable layer on a surface of a substantially tubular polymer; exposing the biostable layer to temperature sufficiently elevated to remove the tubular polymer without substantially affecting the biostable layer; and applying a bioerodible polymer to the biostable layer. In embodiments, the process further includes applying a bioerodible polymer layer onto at least a portion of the biostable layer.

[0014] Further embodiments may include one or more of the following features: at least a portion of the stent degrades over a period of time inside the organism and releases the therapeutic agent; and/or the stent is implanted in a cardiovascular passageway.

[0015] An erodible or bioerodible medical device, e.g., a stent, refers to a device, or a portion thereof, that exhibits substantial mass or density reduction or chemical transformation, after it is introduced into a patient, e.g., a human patient. Mass reduction can occur by, e.g., dissolution of the material that forms the device and/or fragmenting of the device. Chemical transformation can include oxidation/reduction, hydrolysis, substitution, electrochemical reactions, addition reactions, or other chemical reactions of the material from which the device, or a portion thereof, is made. The erosion can be the result of a chemical and/or biological interaction of the device with the body environment, e.g., the body itself or body fluids, into which it is implanted and/or erosion can be triggered by applying a triggering influence, such as a chemical reactant or energy to the device, e.g., to increase a reaction rate. For example, a device, or a portion thereof, can be formed from an active metal, e.g., Mg or Ca or an alloy thereof, and which can erode by reaction with water, producing the corresponding metal oxide and hydrogen gas (a redox reaction). For example, a device, or a portion thereof, can be formed from an erodible or bioerodible polymer, or an alloy or blend erodible or bioerodible polymers which can erode by hydrolysis with water. The erosion occurs to a desirable extent in a time frame that can provide a therapeutic benefit. For example, in embodiments, the device exhibits substantial mass reduction after a period of time which a function of the device, such as support of the lumen wall or drug delivery is no longer needed or desirable. In particular embodiments, the device exhibits a mass reduction of about 10 percent or more, e.g. about 50 percent or more, after a period of implantation of one day or more, e.g. about 60 days or more, about 180 days or more, about 600 days or more, or 1000 days or less. In embodiments, the device exhibits fragmentation by erosion processes. The fragmentation occurs as, e.g., some regions of the device erode more rapidly than other regions. The faster eroding regions become weakened by more quickly eroding through the body of the endoprosthesis and fragment from the slower eroding regions. The faster eroding and slower eroding regions may be random or predefined. For example, faster eroding regions may be predefined by treating the regions to enhance chemical reactivity of the regions. Alternatively, regions may be treated to reduce erosion rates, e.g., by using coatings. In embodiments, only portions of the device exhibits erodibilty. For example, an exterior layer or coating may be erodible, while an interior layer or body is non-erodible. In embodiments, the endoprosthesis is formed from an erodible material dispersed within a non-erodible material such that after erosion, the device has increased porosity by erosion of the erodible material.

[0016] Erosion rates can be measured with a test device suspended in a stream of Ringer's solution flowing at a rate of 0.2 m/second. During testing, all surfaces of the test device can be exposed to the stream. For the purposes of this disclosure, Ringer's solution is a solution of recently boiled distilled water containing 8.6 gram sodium chloride, 0.3 gram potassium chloride, and 0.33 gram calcium chloride per liter.

[0017] Aspects and/or embodiments may have one or more of the following additional advantages. The presence of a biostable layer in a bioerodible medical device offers several advantages including one or more of: providing a firm substrate to an otherwise eroding structure, thus facilitating endothelial cell growth and/or attachment while retaining sufficient flexibility to facilitate stent delivery and deployment; providing a biostable layer that offers increased flexibility for tailoring a stent surface (e.g., tailoring one or more of: texture, thickness, functional group attachment and/or formation of molecule-sized cavities upon removal of organic templates or “molecular imprinting”); and/or controlling erosion (e.g., bioerosion) of the endoprosthesis by protecting the underlying structure from corrosion. By placing one or more biostable layers at predetermined locations, the rate of erosion of different portions of the endoprosthesis can be controlled. Release of a therapeutic agent from the endoprosthesis can be controlled as the rate of erosion is controlled. Moreover, the visibility of the endoprosthesis, e.g., biodegradable endoprosthesis, to imaging methods, e.g., X-ray and/or Magnetic Resonance Imaging (MRI), can be enhanced, even after the endoprosthesis is partly eroded, by e.g., incorporating a radiopaque material into the biostable layer.

[0018] Other aspects, features, and advantages will be apparent from the description and drawings, and from the claims.

[0026] Like reference symbols in the various drawings indicate like elements.

[0027] Referring to FIGS. 1A-1B, the stent 10 is generally a tubular device defined by a stent wall 21 including fenestrations 22 separated by struts 23. Referring as well to FIG. 1B, a cross-section through the stent wall, a thin continuous biostable layer 11 is provided on the outside of an erodible layer 25. In this embodiment, the bioerodible layer is eroded by exposure to bodily fluid from the interior of the stent, while the biostable layer provides a firm structure to enhance endothelization and reduce dislodgement of fragments of the bioerodible layer. Referring to FIGS. 2A-2D, in use, stent 10 is placed over a balloon 15 carried near the distal end of a catheter 14, and is directed through a lumen 16 (FIG. 2A) until the portion carrying the balloon and stent reaches the region of an occlusion 18. The stent 10 is then radially expanded by inflating the balloon 15 and pressed against the vessel wall with the result that occlusion 18 is compressed (FIG. 2B). The vessel wall surrounding the stent 10 undergoes a radial expansion (FIG. 2B). The pressure is then released from the balloon 15, and the catheter 14 is withdrawn from the vessel (FIG. 2C). Over time, the underlying structure 25 of the stent 10 erodes in the body, sometimes creating fragments 19. The biostable layer 11 remains leaving a firm structure for endothelization from the lumen wall which envelopes the stent and, to some extent, reducing erosion and/or dislodgement of the fragments (FIG. 2D).

[0028] Referring to FIGS. 3A and 3B, in another embodiment, stent 30 having a non-continuous biostable layer 31 on top of a bioerodible underlying structure 35 is illustrated before and after exposure to external fluids, respectively. The non-continuous layer 31 defines a window 32 through which the bioerodible structure is exposed to the body from the exterior of the stent. Prior to exposure to the bodily fluids, the bioerodible underlying structure 35 is substantially intact (FIG. 3A). Over time, portion(s) of the underlying structure 35 exposed to external fluids erode at a faster rate than the corresponding areas covered by the biostable layer 31, thus creating a differentially fragmented stent structure (FIG. 3B).

[0029] The underlying stent structure can include one or more bioerodible materials chosen from, e.g., a bioerodible metal, a bioerodible metal alloy, or a bioerodible non-metal. In particular embodiments, the stent structure has an overall thickness, stiffness and other mechanical properties sufficient to maintain the patency of the occluded region of a lumen after an angioplasty procedure. As the erodible structure degrades over time, the wall thickness is reduced and the flexibility of the stent is increased. Endothelization of the erodible structure may be typically inhibited by the continuous erosion. The biostable layer provides a non-eroding surface on which cell growth can occur. The biostable layer is sufficiently flexible, e.g., because of its thinness, so that it does not substantially inhibit the mechanical properties of the stent needed for delivery and deployment or inhibit the natural motion of the blood vessel. The biostable layer can also be textured to enhance endothelization. The biostable layer can be provided, and textured morphologies can be formed, by low temperature processes, such as sol-gel processes.

[0030] In particular embodiments, the biostable material is a ceramic and the bioerodible material is a polymer. The biostable layer typically makes up about 50%, 20%, 10% or less of the wall thickness of the stent at implantation, e.g., about 5%, 1%, 0.5%, or 0.05% or less of the wall thickness of the stent at implantation. Typically, the relative thinness of the biostable layer is adjusted such that the stent retains the flexibility needed for stent delivery and deployment. The stent typically retains at least about 50%, 75%, 90% or more of the flexibility of a stent otherwise identical but without the biostable layer. The flexibility of the stent can be measured by techniques known in the art. For example, the stent can be expanded into a silicon rubber test tube with similar mechanical properties as a blood vessel. After expansion, the change in flexibility of the stented vessel area can be measured by bending the vessel in a three-point bend test. The three-point bend test is known in the art as a way of evaluating stent stiffness (or its reciprocal, flexibility). It typically involves determining the slope of a force-displacement curve by measuring the stent deflection when the sent is secured by two end-points at a predetermined distance apart, e.g., 20 mm apart, and applying a vertical force or traction midway between the two secured end-points (e.g., applying a force to a hook suspended by an Instron), which provides the third point of the three-point bend test. The three-point bend test is described further in Ormiston, J. et al. (2000) Catherization and Cardiovascular Interventions 50:120-124. Alternatively, the bending of the stent on the balloon catheter can be measured, e.g., by performing a track test. Track testing is known in the art, and is described, for example, in paragraphs 47-53 of U.S. 2004-0210211.

[0031] Examples of ceramics include metal oxides, e.g., oxides that include one or more of titanium oxide, ruthenium oxide or iridium oxide. For example, one or more layers of titanium oxide can be used because of its good biocompatibility and induction of endothelization. Titanium oxide can be used in crystalline or amorphous form. Crystalline forms can enhance attachment and/or growth of endothelial cells. Titanium oxides are discussed further in Chen, J. Y., Wan, G. J. (2004) Surface & Coating Technology 186:270-276. The thickness of the biostable layer can vary as needed, but is typically substantially thin to provide a flexible stent structure to facilitate, e.g., stent deployment, while providing a substantially firm substrate to facilitate endothelization. Typically, the biostable layer 11 has a thickness in the range of less than 1000 nm, typically less than 100 nm microns, and about 1 to 50 nm, more typically, about 10 to 20 nm. The biostable layer can have a volume an average volume in the range of about 2,000 to 30,000, more typically 5,000 to 20,000 cubic micrometer per square millimeter of stent surface area. The volume can be measured, e.g., indirectly by statistically making a line measurement along the stent surface using, for example, atomic force microscopy (AFM), or focused ion beam to produce cross-sections along lines. Alternatively, field emission scanning electron microscopy (FSEM) can be used to examine the surface topology and/or the percentage of the stent surface that is covered with the biostable layer. The biostable layer 11 can extend over an entire surface of the stent 10 (e.g., an inner or outer surface, or a side wall, or any combination thereof), or can cover a portion of the stent (e.g., 25%, 50%, 75% of the length of the stent surface).

[0032] The biostable layer can coat one or more of the interior or exterior stent surfaces and/or sidewalls, leaving the abluminal surface exposed. In embodiments, the interior surface is coated. Selected portions of the biostable layer can be removed as desired using, for example, a laser to control the rate and/or location of erosion. The stent can have one, two or more layers of biostable materials as desired. In other embodiments, one or more layers of biostable materials can be embedded with one or more bioerodible materials (e.g., organic, polymeric, biological or metallic materials), thus forming a multi-layered hybrid structure.

[0033] The biostable layer offers additional advantages, such as allowing tailoring of the stent surface (e.g., tailoring of one or more of: texture, thickness, functional group attachment and/or molecular imprinting by forming molecule-sized cavities upon removal of organic templates). Referring to FIGS. 4A-4B, a perspective view of a stent 40 having a textured surface 41, and a cross-sectional view of the region A in FIG. 4A, respectively, the biostable layer 45 can have a texture (also referred to herein as “nanotexture”) characterized by a plurality of nodules 44 that facilitates endothelial cell migration and/or attachment. Referring to FIG. 5, a scanning electron microscopy (SEM) micrograph of an exemplary high magnification top view of a textured surface titania layer shows a spherical grain morphology of a plurality of nodules about 15-20 nm in size (scale bar in FIG. 5 corresponds to about 70 nm). Surface morphologies of ceramic layers are described further in Daoud, W. et al. (2005) Journal of Non-Crystalline Solids 351:1486-1490. The nodule diameter is typically less than 100 nm, e.g., less than 50 nm, typically about 5 to 30 nm, more typically about 10 to 20 nm. The texture defines spaces between the nodules of about 50 to 500 nm, e.g., around 200 nm, or about the size of a typical endothelial cell. Textured coatings enhance growth and migration of both smooth muscle and endothelial cells. In order to reduce smooth muscle coverage, the textured biostable layer can include a drug that preferentially inhibits smooth muscle cell growth, e.g., paclitaxel, thereby maximizing endothelial cell coverage of the stent.

[0034] The biostable layer can be formed by sol-gel processes. Sol-gel processes, in particular, low temperature sol-gel process, are useful for creating a crystalline metal oxide coating on a polymeric substrate (Daoud, W. et al. (2005) supra; Yun, Y-J et al. (2004) Materials Letters 58:3703-3706; Nishio, K. et al. (1999) Thin Solid Films 350:96-100; Wu, L. et al. (2005) Journal of Solid State Chemistry 178:321-328). In embodiments, the metal oxide is applied to the polymer. In other embodiments, the polymer is applied to the metal oxide. Sol gel processes can form thin coatings, without excessive heating which could destroy the polymer or other substrates. For example, crystalline titanium dioxide (TiO₂) thin films can be deposited onto an erodible stent at low temperatures using a sol-gel dip-coating method. The titania sol can be prepared, for example, at room temperature by mixing titanium tetraisopropoxide (TTIP) in acidic aqueous solutions and subsequently refluxed at 80° C. for 8 hours to facilitate the formation of anatase crystallites. The deposited titanium oxide films can be heated at 115° C. Homogeneous surfaces of spheroids typically about 20-60 nm in size can be formed. One or more biostable layers of iridium oxide can be prepared by, e.g., a sol-gel dip-coating process where iridium chloride is used as the starting material. The coating solution can also be prepared by reacting iridium chloride, ethanol and acetic acid as described in Nishio, K. et al. (1999) supra. Sol-solvothermal processes can be used to form mesoporous nanocrystalline titanium dioxide with photocatlytic activity as described in Wu et al. (2005) supra. In embodiments, the deposition of the biostable layers is carried out at room temperature.

[0035] A surface sol-gel process involving a layer-by-layer approach can be used to add one or more monolayers of metal oxides, organic, polymeric, and/or biological materials (e.g., peptides such as RGD peptides to promote endothelial cell binding) (see e.g., Kunitake, T., Lee, S-W. (2004) Analytica Chimica Acta 504:1-6).

[0036] Referring to FIG. 6, a general scheme of surface sol-gel process shows a solid substrate with hydroxyl groups on its surface, which is allowed to react with metal alkoxides in solution to form a covalently-bound surface monolayer of the metal alkoxide. The excessively adsorbed alkoxide can be removed by rinsing. The chemisorbed alkoxide monolayer is then hydrolyzed to give a new hydroxylated surface. The thickness of the metal oxide layer can be as thin as about 1 nm. In embodiments, the polyhydroxyl compounds adsorbed on the surface provide free hydroxyl groups, and metal alkoxides are subsequently adsorbed. The process can be repeated as desired to form one or more multilayers of the same or different materials, e.g., other metal oxides, organic materials (e.g., functional groups), polymeric materials, and/or biological materials (e.g., peptides). The biostable layer can be derivatized as desired by altering the compositions of the layers, thus creating functionalized groups and/or selective molecular imprinting sites. For example, organic polyhydroxyl compounds (e.g., carboxylic acids) can be readily incorporated onto a surface of a metal oxide layer. Upon removal of the organic template, molecule-sized cavities are formed imprinting a cavity that reflects the structural and enantioselective features of the template. The biostable layer can be derivatized further, e.g., to include biodegradable polymers to create surface features that enhance endothelial cell function. For example, biodegradable polymers, such as polylactic acid and/or polyglycolic acid (e.g., poly(lactic-co-glycolic acid) (PLGA)) can be used as scaffolds to support endothelial cell attachment. Suitable techniques are described in Miller, D. C. et al. (2004) Biomaterials 25:53-61. Since the attachment of both smooth muscle and endothelial cells is typically increased using PLGA, the polymer may optionally include an inhibitor of smooth muscle cells, such as paclitaxel.

[0037] The biostable layer can be applied to the stent before or after adding the bioerodible structure. For example, the biostable layer can be applied to the stent prior to forming the bioerodible structure. In those embodiments, the biostable layer(s) (e.g., ceramic layer) can be exposed to high temperatures before it is connected to the bioerodible structure.

[0038] Referring to FIGS. 7A-7F, perspective and cross-sectional views of the stent undergoing coating steps 7A-7E (upper and lower panels, respectively), starting from step 7A, a solid polymer of tubular shape 50 (e.g., a tube made of nylon, poly(ethylene oxide), polyimine (PI)) having a substantially smooth surface is shown. Referring to FIG. 7B, a stent pattern 54 can be formed on the polymer tube 50, e.g., by writing the stent shape on the polymer tube 50 using an ink pen containing a thick sol-gel solution. In other embodiments, a metallic solution can be used to write a metallic layer on the polymer tube. Ink pens are commercially available from Ohm Craft, Honeoye Falls, N.Y. under the registered mark MicroPen®. Referring back to FIG. 7B and FIG. 7C, by applying heating conditions according to ceramic specifications, a titanium oxide coating is converted into an anatase state (e.g., by heating the polymer to about 500° C. for about 6 hours) and the polymer tube is eliminated, thereby resulting in a very thin biostable (e.g., ceramic) film 56 in the shape of the stent. The biostable film 56 can then be fitted inside a cylindrical tube (not shown) with an inner diameter the size of the desired inner diameter of the final stent and an outer diameter slightly larger than the biostable (e.g., ceramic) film 56. Referring to FIG. 7D, a bioerodible polymer is deposited within the cylindrical tube, resulting in a bioerodible tube 58 with a biostable (e.g., ceramic) layer 56 having a stent shape embedded within. Portions of the bioerodible tube 58 can be selectively removed, e.g., using an excimer laser to ablate the polymer, thereby forming a coated ceramic film 60 (i.e., a ceramic film 56 coated with a biodegradable layer 58). Referring back to FIG. 7D, the removal can be done, for example, by aiming the laser radially to the bioerodible tube 58 and focusing the laser in a number steps to the whole cylinder at a fluence level which is high enough to ablate the polymer, but lower than the ablation threshold of the biostable, e.g., ceramic, film 56. The biodegradable polymer 58 adjacent to the biostable, e.g., ceramic, film 56 will remain substantially intact as it is in the shadow of the biostable, e.g., ceramic, film. Referring to FIG. 7E, the polymer in between can be ablated, thus resulting in a stent 60 made of a biodegradable polymer 58 with a biostable, e.g., ceramic, outer film 56. Referring to FIG. 7F, further embodiments (optionally) include applying (e.g., spraying) to the stent 60 of FIG. 7E, one or more layers of a bioerodible polymer (e.g., the same or different bioerodible polymer as the one used to form the bioerodible tube 58), such that the biostable (e.g., ceramic) film 56 is embedded (fully or a portion thereof) within a thin bioerodible polymeric film 58. In the embodiment shown in FIG. 7F, the same bioerodible polymer is applied to the stent 60 as the one used in FIGS. 7D-7E. The bioerodible polymer is expected to degrade in the body at a fast rate, however it is expected to reduce the propensity of the biostable ceramic layer to break off after expansion.

[0039] Referring back to FIG. 7A-7F, the biostable, e.g., ceramic, layer can be further altered to enhance the bond between the bioerodible and the biostable layers. In embodiments, a plurality of indentations or markings can be formed on stent pattern 54, using, for example, an excimer laser. Such indentations or markings will create pitts on the inside of the ceramic shape once the firing has taken place, thus enhancing the bond between the biodegradable polymer and the biostable, e.g., ceramic, layer.

[0040] In embodiments, the biostable layer can be used for corrosion protection when the bioerodible underlying structure of the stent is a bioerodible metal, such as magnesium, iron, and nickel (Cheng, F. T. et al. (2004) Scripta Materilia 51:1041-1045; Atik, M. et al. (1995) Ceramics International 21:403-406). Other coatings that can be used to form thin layers by sol-gel for corrosion protection include zirconium dioxide (ZrO₂), binary compositions of titanium dioxide and silicon dioxide (TiO₂—SiO₂), and aluminium oxide and silicon dioxide (Al₂O₃—SiO₂) (Atik, M. et al. (1995) supra).

[0041] The stent may additionally include one or more biostable materials in addition to one or more biostable layer described above. Examples of biostable materials include stainless steel, tantalum, niobium, platinum, nickel-chrome, cobalt-chromium alloys such as Elgiloy® and Phynox®, Nitinol (e.g., 55% nickel, 45% titanium), and other alloys based on titanium, including nickel titanium alloys, thermo-memory alloy materials. Stents including biostable and bioerodible regions are described, for example, in US 2006-0122694, entitled “Medical Devices and Methods of Making the Same.” The material can be suitable for use in, for example, a balloon-expandable stent, a self-expandable stent, or a combination of both (see e.g., U.S. Pat. No. 5,366,504). The components of the medical device can be manufactured, or can be obtained commercially. Methods of making medical devices such as stents are described in, for example, U.S. Pat. No. 5,780,807, and U.S. Patent Application Publication No. 2004-0000046-A1, both of which are incorporated herein by reference. Stents are also available, for example, from Boston Scientific Corporation, Natick, Mass., USA, and Maple Grove, Minn., USA.

[0042] Bioerodible materials are described, for example, in U.S. Pat. No. 6,287,332 to Bolz; U.S. Patent Application Publication No. US 2002/0004060 A1 to Heublein; U.S. Pat. Nos. 5,587,507 and 6,475,477 to Kohn et al., the entire contents of each of which is hereby incorporated by reference. Examples of bioerodible metals include alkali metals, alkaline earth metals (e.g., magnesium), iron, zinc, and aluminum. Examples of bioerodible metal alloys include alkali metal alloys, alkaline earth metal alloys (e.g., magnesium alloys), iron alloys (e.g., alloys including iron and up to seven percent carbon), zinc alloys, and aluminum alloys. Examples of bioerodible non-metals include bioerodible polymers, such as, e.g., polyanhydrides, polyorthoesters, polylactides, polyglycolides, polysiloxanes, cellulose derivatives and blends or copolymers of any of these. Bioerodible polymers are disclosed in U.S. Published Patent Application No. 2005/0010275, filed Oct. 10, 2003; U.S. Published Patent Application No. 2005/0216074, filed Oct. 5, 2004; and U.S. Pat. No. 6,720,402, the entire contents of each of which is incorporated by reference herein.

[0043] The stent can be manufactured, or the starting stent can be obtained commercially. Methods of making stents are described, for example, in U.S. Pat. No. 5,780,807 and U.S. Application Publication US-2004-0000046-A1. Stents are also available, for example, from Boston Scientific Corporation, Natick, Mass., USA, and Maple Grove, Minn., USA. The stent can be formed of any biocompatible material, e.g., a metal or an alloy, as described herein. The biocompatible material can be suitable for use in a self-expandable stent, a balloon-expandable stent, or both. Examples of other materials that can be used for a balloon-expandable stent include noble metals, radiopaque materials, stainless steel, and alloys including stainless steel and one or more radiopaque materials.

[0044] The endoprosthesis, e.g., the stent, can, further include at least one therapeutic agent present in the biostable and/or bioerodible portion of the stent. If the therapeutic agent is found in the bioerodible portion of the stent (e.g., interspersed throughout or localized to a predetermined site), release of the therapeutic agent can be controlled as the bioerodible portion of the stent erodes. The terms “therapeutic agent”, “pharmaceutically active agent”, “pharmaceutically active material”, “pharmaceutically active ingredient”, “drug” and other related terms may be used interchangeably herein and include, but are not limited to, small organic molecules, peptides, oligopeptides, proteins, nucleic acids, oligonucleotides, genetic therapeutic agents, non-genetic therapeutic agents, vectors for delivery of genetic therapeutic agents, cells, and therapeutic agents identified as candidates for vascular treatment regimens, for example, as agents that reduce or inhibit restenosis. By small organic molecule is meant an organic molecule having 50 or fewer carbon atoms, and fewer than 100 non-hydrogen atoms in total.

[0045] The therapeutic agent can be chosen from one or more of, e.g., an anti-thrombogenic agent, an anti-proliferative/anti-mitotic agents, an inhibitor of smooth muscle cell proliferation, an antioxidant, an anti-inflammatory agent, an anesthetic agents, an anti-coagulant, an antibiotic, or an agent that stimulates endothelial cell growth and/or attachment. Exemplary therapeutic agents include, e.g., anti-thrombogenic agents (e.g., heparin); anti-proliferative/anti-mitotic agents (e.g., paclitaxel, 5-fluorouracil, cisplatin, vinblastine, vincristine, inhibitors of smooth muscle cell proliferation (e.g., monoclonal antibodies), and thymidine kinase inhibitors); antioxidants; anti-inflammatory agents (e.g., dexamethasone, prednisolone, corticosterone); anesthetic agents (e.g., lidocaine, bupivacaine and ropivacaine); anti-coagulants; antibiotics (e.g., erythromycin, triclosan, cephalosporins, and aminoglycosides); agents that stimulate endothelial cell growth and/or attachment. Therapeutic agents can be nonionic, or they can be anionic and/or cationic in nature. Therapeutic agents can be used singularly, or in combination. Preferred therapeutic agents include inhibitors of restenosis (e.g., paclitaxel), anti-proliferative agents (e.g., cisplatin), and antibiotics (e.g., erythromycin). Additional examples of therapeutic agents are described in U.S. Published Patent Application No. 2005/0216074, the entire disclosure of which is hereby incorporated by reference herein.

[0046] To enhance the radiopacity of stent, a radiopaque material, such as gold nanoparticles, can be incorporated into endoprosthesis, e.g., the biostable layer or the stent body. For example, gold nanoparticles can be made positively charged by applying a outer layer of lysine to the nanoparticles, e.g., as described in “DNA Mediated Electrostatic Assembly of Gold Nanoparticles into Linear Arrays by a Simple Dropcoating Procedure” Murali Sastrya and Ashavani Kumar, Applied Physics Letters, Vol. 78, No. 19, 7 May 2001. Other radiopaque materials include, for example, tantalum, platinum, palladium, tungsten, iridium, and their alloys.

[0047] Medical devices, in particular endoprostheses, as described above include implantable or insertable medical devices, including catheters (for example, urinary catheters or vascular catheters such as balloon catheters), guide wires, balloons, filters (e.g., vena cava filters), stents of any desired shape and size (including coronary vascular stents, aortic stents, cerebral stents, urology stents such as urethral stents and ureteral stents, biliary stents, tracheal stents, gastrointestinal stents, peripheral vascular stents, neurology stents and esophageal stents), grafts such as stent grafts and vascular grafts, cerebral aneurysm filler coils (including GDC-Guglilmi detachable coils-and metal coils), filters, myocardial plugs, patches, pacemakers and pacemaker leads, heart valves, and biopsy devices. In one embodiment, the medical device includes a catheter having an expandable member, e.g., an inflatable balloon, at its distal end, and a stent or other endoprosthesis (e.g., an endoprosthesis or stent as described herein). The stent is typically an apertured tubular member (e.g., a substantially cylindrical uniform structure or a mesh) that can be assembled about the balloon. The stent typically has an initial diameter for delivery into the body that can be expanded to a larger diameter by inflating the balloon. The medical devices may further include drug delivery medical devices for systemic treatment, or for treatment of any mammalian tissue or organ.

[0048] The medical device, e.g., endoprosthesis, can be generally tubular in shape and can be a part of a stent. Simple tubular structures having a single tube, or with complex structures, such as branched tubular structures, can be used. Depending on specific application, stents can have a diameter of between, for example, 1 mm and 46 mm. In certain embodiments, a coronary stent can have an expanded diameter of from about 2 mm to about 6 mm. In some embodiments, a peripheral stent can have an expanded diameter of from about 4 mm to about 24 mm. In certain embodiments, a gastrointestinal and/or urology stent can have an expanded diameter of from about 6 mm to about 30 mm. In some embodiments, a neurology stent can have an expanded diameter of from about 1 mm to about 12 mm. An abdominal aortic aneurysm (AAA) stent and a thoracic aortic aneurysm (TAA) stent can have a diameter from about 20 mm to about 46 mm. Stents can also be preferably bioerodible, such as a bioerodible abdominal aortic aneurysm (AAA) stent, or a bioerodible vessel graft.

[0049] In some embodiments, the medical device, e.g., endoprosthesis, is used to temporarily treat a subject without permanently remaining in the body of the subject. For example, in some embodiments, the medical device can be used for a certain period of time (e.g., to support a lumen of a subject), and then can disintegrate after that period of time. Subjects can be mammalian subjects, such as human subjects (e.g., an adult or a child). Non-limiting examples of tissues and organs for treatment include the heart, coronary or peripheral vascular system, lungs, trachea, esophagus, brain, liver, kidney, bladder, urethra and ureters, eye, intestines, stomach, colon, pancreas, ovary, prostate, gastrointestinal tract, biliary tract, urinary tract, skeletal muscle, smooth muscle, breast, cartilage, and bone.

[0050] All publications, patent applications, patents, and other references mentioned herein are incorporated by reference herein in their entirety.

[0051] Other embodiments are within the scope of the following claims.