AU2008201081B8

AU2008201081B8 - Valvular prostheses having metal or pseudometallic construction and methods of manufacture

Info

Publication number: AU2008201081B8
Application number: AU2008201081A
Authority: AU
Inventors: Steven R. Bailey; Christopher E. Banas; Christopher T. Boyle; Christina Fuss; Denes Marton; Julio C. Palmaz; Eugene A. Sprague; Roger W. Wiseman
Original assignee: ABPS Venture One Ltd
Current assignee: ABPS Venture One Ltd
Priority date: 1999-12-31
Filing date: 2008-03-06
Publication date: 2011-03-10
Anticipated expiration: 2020-12-18
Also published as: AU2008201080B2; AU2008201081B2; AU2008201080B8; AU2008201080A1; AU2008201081A1

Description

P/00/011 Regulation 3.2 AUSTRALIA Patents Act 1990 ORIGINAL COMPLETE SPECIFICATION STANDARD PATENT Invention Title: "VALVULAR PROSTHESES HAVING METAL OR PSEUDOMETALLIC CONSTRUCTION AND METHODS OF MANUFACTURE' The following statement is a full description of this invention, including the best method of performing it known to me/us: VALVULAR PROSTHESES HAVING METAL OR PSEUDOMETALLIC CONSTRUCTION AND METHODS OF MANUFACTURE Background of the Invention 5 Any discussion of the prior art throughout the specification should in no way be considered as an admission that such prior art is widely known or forms part of common general knowledge in the field. The present invention relates generally to metal and pseudometallic films suitable for implantation into mammalian subjects in need thereof More particularly, 10 the present invention pertains to prosthetic cardiac and venous valve implants, access ports and other implantable medical devices that employ moveable valve flaps. The implantable medical devices according to the present invention have improved valve flap members fabricated from metal and/or pseudometallic materials. It is desirable, although not essential to the present invention, that the prosthetic cardiac and venous iS valve implants be capable of being delivered using endovascular techniques and being implanted at an intracardiac or intravenous site without the need for anatomic valve removal. Embodiments of the prosthetic valves of the present invention are well-suited for cardiac delivery via a femoral or subclavian artery approach using a delivery catheter, and, depending upon the specific configuration selected, may be deployed 20 within the heart to repair valve defects or disease or septal defects or disease. According to one embodiment of the invention, there is provided a chamber-to-vessel (CV) configuration that is particularly well suited as an aortic valve prosthesis to facilitate blood flow from the left ventricle to the aorta. In a second embodiment, there is provided a prosthetic valve in a chamber-to-chamber (CC) configuration that is 25 particularly well-adapted for mitral valve replacement or repair of septal defects. Finally, a third embodiment is provided in a vessel-to-vessel (VV) configuration, which is well suited for venous valve exclusion and replacement. Common to each of the CV, CC and VV embodiments of the present invention are a stent support member, a graft member which covers at least a portion of either or 30 both the luminal and abluminal surfaces of the stent and valve flap members. Both the graft member and the valve flap members are preferably fabricated from metallic and/or pseudometallic materials. the valve flaps being coupled to the stent in a manner which - la biases the valve flaps so they close upon a zero pressure differential across the valve region.

More specifically, the valve flap members and the graft members of the present invention are fabricated entirely of self-supporting films made of biocompatible metals or biocompatible pseudonetals. For purposes of this application, the term pseudometal" or "pseudometalie" is intended to mean a biocompatible material which exhibits biological response and material characteristics substantially the same as biocompatible metals, such as 5 for example composite materials. As opposed to wrought materials that are made of a single metal or alloy, the inventive valve flap members and graft members are made of at least two layers formed upon one another into a self-supporting laminate structure. Laminate structures are generally known to increase the mechanical strength of sheet materials, such as wood or paper 10 products. Laminates are used in the field of thin film fabrication also to increase the mechanical properties of the thin film, specifically hardness and toughness. Laminate metal foils have not been used or developed because the standard metal fonning technologies, such as rolling and extrusion, for example, do not readily lend themselves to producing laminate structures. Vacuum deposition technologies can be developed to yield laminate metal 15 structures with improved mechanical properties. In addition, laminate structures can be designed to provide special qualities by including layers that have special properties such as superelasticity, shape memory, radio-opacity, corrosion resistance etc. It is important for the present invention to provide orientational definitions. For purposes of the present invention, references to positional aspects of the present invention 20 will be defined relative to the directional flow vector of blood flow through the implantable device. Thus, the term "proximal" is intended to mean on the inflow or upstream flow side of the device, while "distal" is intended to mean on the outflow or downstream flow side of the device. With respect to the catheter delivery system described herein, the term proximall" is intended to mean toward the operator end of the catheter, while the tenn 25 "distal" is intended to mean toward the terminal end or devico-carrying end of the catheter. Conventional metal foils, wires and thin-walled seamless tubes are typically produced from ingots in a series of hot or cold forming steps that include some combination of rolling, pulling, extrusion and other similar processes. Each of these processing steps is accompanied by auxiliary steps that include cleaning the surftces of the material of foreign 30 material residues deposited on the material by the tooling and lubricants used in the metal -2forming processes. Additionally, chemical interaction with tooling and lubricant materials and ambient gases also introduces contaminants. Some residue will still usually remain on the surface of the formed material, and there is a high probability that these contaminating residues become incorporated during subsequent processing steps into the bulk of the wrought metal product. With decreasing material product size, the significance of such 5 contaminating impurities increases. Specifically, a greater number of process steps, and, therefore, a greater probability for introducing contaminants, are required to produce smaller product sizes. Moreover, with decreasing product size, the relative size of non-metal or other foreign inclusions becomes larger. This effect is particularly important for material thicknesses that are comparable to the grain or inclusion size. For example, austenitic 10 stainless steels have typical grain sizes on the order of magnitude of 10-100 micrometer. When a wire or foil with a thickness in this range is produced, there is significant probability that some grain boundaries or defects will extend across a large portion or even across the total thickness of the product. Such products will have locally diminished mechanical and corrosion resistance properties. While corrosion resistance is remedied by surface treatments 15 such as electropolishing, the mechanical properties are more difficult to control. The mechanical properties of metals depend significantly on their microstructure. The forming and shaping processes used to fabricate metal foils, wires and thin-walled seamless tubes involves heavy deformation of a bulk material, which results in a heavily strained and deformed grain structure. Even though annealing treatments may partially 20 alleviate the grain deformation, it is typically impossible to revert to well-rounded grain structure and a large range of grain sizes is a common result. The end result of conventional forming and shaping processes, coupled with annealing, typically results in non-uniform grain structure and less favorable mechanical properties in smaller sized wrought metal products. It is possible, therefore, to produce high quality homogeneous materials for special 25 purposes, such as micromechanical devices and niedical devices, using vacuum deposition technologies. In vacuum deposition technologies, materials are formed directly in the desired geometry, e.g., planar, tubular, etc. The common principle of the vacuum deposition processes is to take a material in a minimally processed form, such as pellets or thick foils 30 (the source material) and atomize them. Atomization may be carried out using heat, as is the -3case in physical vapor deposition, Or using the effect of collisional processes, as in the case of' sputter deposition, for example. In some forms of deposition, a process, such as laser ablation, which creates microparticles that typically consist of one or more atoms, may replace atomization; the number of atoms per particle may be in the thousands or more. The atoms or particles of the source material are then deposited on a substrate or mandrel to 5 directly fom the desired object. In other deposition methodologies, chemical reactions between ambient gas introduced into the vacuum chamber, i.e., the gas source, and the deposited atoms and/or particles are part of the deposition process. The deposited material includes compound species that are formed due to the reaction of the solid source and the gas source, such as in the case of chemical vapor deposition. In most cases, the deposited 10 material is then either partially or completely removed from the substrate, to form the desired product. The rate of film growth is a significant parameter of vacuum deposition processes. In order to deposit mateiials that can be compared in functionality with wrought metal products, deposition rates in excess of 1. micrometers/hour are a must and indeed rates as high as 100 15 micrometers per hour are desirable. These are high deposition rates and it is known that at such rates the deposits always have a columnar structure, Depending on other deposition parameters, and most importantly on the substrate temperature, the columns may be amorphous or crystalline but at such high deposition rates microcrystalline structure development can be expected at best. The dificulty is that the columns provide a 20 mechanically weak structure in which crack propagation can occur uninhibited across the whole thickness of the deposit. A special advantage of vacuum deposition technologies is that it is possible to deposit layered materials and thus films possessing exceptional qualities may be produced (cf., H. Holleck, V. Schier: "Multilayer PVD coatings for wear protection", Swface and Coatings 25 Technology, Vol. 76-77 (1995) pp. 328-336). Laycred materials, such as superstructures or multilaycrs, arc commonly deposited to take advantage of some chemical, electronic, or optical property of the material as a coating; a common example is an antireflective coating on an optical lens. It has not been recognized until relatively recently that multilayer coatings may have 30 improved mechanical propertics compared with similar coatings made of a single layer. The -4improved mechanical properties may be due to the ability of the interface between the layers to relieve stress. This stress relief occurs if the interface provides a slide plan, is plastic, or may delaminate locally. This property of multilayer films has been recognized in regard with their hardness but this recognition has not been translated to other mechanical properties that are significant for metal products that may be used in application where they replace wrought 5 metal parts. A technological step that interrupts the im growth. results in discontinuous columns and prevents crack propagation across the entire film thickness. In this sense, it is not necessary that the structure consist of a multiplicity of chemically distinct layers, as it is common in the case of thin film technology where multilayers are used. Such chemical 10 differences maybe useful and may contribute to improved properties of the materials. As used in this application a "layer" is intended to mean a substantially uniform material limited by interfaces between it and adjacent other substantially homogeneous layers, substrate, or environment. The interface region between adjacent layers is an inhomogeneous region in which extensive thermodynamic parameters may change. Different 15 layers are not necessarily characterized by different values of the extensive thermodynamic parameters but at the interface, there is a local change at least in some parameters. For example, the interface between two steel layers that are identical in composition and microstructure may be characterized by a high local concentration of grain boundaries due to an interruption of the film growth process. Thus, the interface between. layers is not 20 necessarily different in chemical composition if it is different in structure, It is necessary to provide for good adhesion between the layers and this is usually achieved by providing for a relatively broad interface region rather than for an abrupt interface. The width of the interface region may be defined as the rangc within which extensive thermodynamic parameters change. This range can depend on the interface area 25 considered and. it may mean the extent of interface microroughness. In other words, adhesion may be promoted by increased interface microroughness between adjacent layers. By providing for a layered structure, the inventive materials consist of a controlled maximum size of grains and columns as extended defects in the direction of the film growth (perpendicular to the layers). This limit of the grain or defect size results in materials that 30 have increased mechanical strength and particularly increased toughness compared to their -6 non-laminated counterparts, both deposited and wrought materials. In addition, limiting the extent to which defects and grain boundaries reach across the laminate, corrosion resistance is also improved. Laminated materials will have additional advantages when chemical 5 compositions of the layers are chosen to achieve special properties. For example, a radiopaque material such as tantalum may form one layer of a structure while other layers are chosen to provide the material with necessary mechanical and other properties. Heretofore, however, conventional implantable valves have traditionally been 1o fabricated of rigid metal or synthetic materials, or have been fabricated of pliant synthetic polymeric materials, each of which involved hoth hemodynarnic and physiological complications. It is an object of the present invention to overcome or ameliorate at least one of the disadvantages of the prior art, or to provide a useful alternative. Is Summary of Prior Art The prior art discloses certain common device segments inherently required by a percutaneous prosthetic valve: an expandable stent segment, an anchoring segment and a flow-regulation segment. 20 Prior art percutaneous prosthetic valve devices include the Dobben valve, U.S. Pat. No. 4,994,077, the Vince valve, U.S. Pat. No. 5,163,953, the Teitelbaum valve, U.S. Pat. No. 5,332,402, the Stevens valve, U.S. Pat. No. 5,370,685, the Pavenik valve, U.S. Pat. No. 5,397,351, the Taheri valve, U.S. Pat. No. 5,824,064, the Anderson valves, U.S. Pat. Nos. 5,411,552 & 5,840,081, the Jayaraman valve, U.S. Pat. No. 5,855,597, the 25 Besseler valve, U.S. Pat. No. 5,855,601, the Khosravi valve, U.S. Pat. No. 5,925,063, the Zadano-Azizi valve, U.S. Pat. No. 5,954,766, and the Leonhardt valve, U.S. Pat. No. 5,957,949. Each of these pre-existing stent valve designs has certain disadvantages which are resolved by the present invention. The Dobben valve has a disk shaped flap threaded on a wire bent like a safety pin 30 to engage the vessel wall and anchor the valve. A second embodiment uses a stent of a cylindrical or crown shape that is made by bending wire into a zig-zag shape to anchor the device and attach the flow regulator flap. The device presents significant hernodynamic, delivery, fatigue and stability disadvantages.

The Vince valve has a stent comprised of a toroidal body formed of a Dexible coil of wire and a flow-regulation mechanism consisting of a flap of biologic material. Numerous longitudinal extensions within the stcnt are provided as attaehmuent posts to mount the flow regulation mechanism. The device requires balloon expansion to deliver to the body orifice. The main shortcoming of this design is delivery profile. Specifically, the device and method 5 put forth will require a 20+ French sizc catheter (approximately 9 French sizes to accommodate the balloon and 14+ French sizes to accommodate the compressed device) making the device clinically ineffective as a minimally invasive technique. Additionally, the device does not adequately address hcmodynamic, stability and anchoring concerns. The Teitelbaum valve is made of shape memory nilinol and consists of two 10 components. The first component is stent-like and comprised of a meshwork or braiding of nitinol wire similar to that described by WaUsten, U.S. Pat. No. 4,655,771, with trumpet like distal a proximal flares. The purpose of the stent is to maintain a semi-ridged patent channel through the diseased cardiac valve after initial balloon dilation. The flared ends are intended to maintain the position of the stent component across the valve thereby anchoring the 15 device. Embodiments for the flow-regulation mechanism include a sliding ohturator and a caged ball both which are delivered secondary to the stent portion. The disadvantages of the device are the flow regulators reduce the effective valve orifice and generate sub-optimal hemodynamic characteristics; fatigue concerns arise from the separate nature of the stem and flow-regulation components; the high metal and exposed metal content raises 20 thrombogenesis, valvular stenosis and chronic anticoagulation concerns; and the separate delivery requirements (although addressing the need for small delivery profile) in addition to any initial valvuloplasty performed increases the time, costs, risks. difficulty and trauma associated with the pemutaneous procedure. The Pavenik valve is a self-expanding percutaneous device comprised of a popped, a 25 stent and a restraining element. The valve stent has barbed means to anchor to the internal passageway. The device includes a self-expanding stent of a zigzag configuration in conjunction with a cage mechanism comprised of a multiplicity of crisscrossed wires and a valve seat. The disadvantages of the device include large delivery profile, reduced cffectivc valvular orifice, possible perivalvular leakage, trauma-inducing turbulent flow generated by 30 the cage occlusive apparatus and valve seat, thronibogenesis, valvular stenosis, chronic -7anticoagulation, problematic physiological and procedural concerns due to the barb anchors and complex delivery procedure that includes inflation of occlusive member after initial implantation. Stevens discloses a percutaneous valve replacement system for the endovascular removal of a malfunctioning valve followed by replacement with a prosthetic valve. The 5 valve replacement system may include a prosthetic valve device comprised of a stent and cusps for flow-regulation such as a fixed porcine aortic valve, a valve introducer, an intraluminal procedure device, a procedure device capsule and a tissue cutter. The devices disclosed indicate a long and complex procedure requiring large diameter catheters. The valve device disclosed will require a large delivery catheter and does not address the key 10 mechanisms required of a functioning valve. Additionally, the device requires intraluminal securing moans such as suturing to anchor the device at the desired location. The Taberi valve describes an aartic valve replacement combined with an aortic arch graft. The devices and percutancous methods described require puncture of the chest cavity. Anderson has disclosed various balloon expandable pcrcutaneous prosthetic valves. 15 The latest discloses a valve prosthesis comprised of a stent made from an expandable cylindrical structure made of several spaced apices and an elastically collapsible valve mounted to the stent with the comniissural points of the valve mounted to the apices. The device is placed at the desired location by balloon expanding the stent and valve. The main disadvantage to this design is the 20+ Prench size delivery requirement. Other problems 20 include anchoring stability, perivalvular leakage, difficult manufacture and suspect valve performance. The Jayaraman valve includes a star-shaped stent and a replacement valve and/or replacement graft for use in repairing a damaged cardiac valve. The device is comprised of a chain of interconnected star-shaped stent scgrents in the center of which sits a replacement 25 valve. The flow-regulation mechanism consists of three flaps cut into a flat piece of grafi material that is rolled to form a conduit in which the three flaps may be folded inwardly in an overlapping manner. An additional flow-regulation mechanism is disclosed in which a patch (or multiple patches) is sutured to the outside of a conduit which is then pulled inside out or inverted such that the patch(s) reside on the fully inverted conduit. A balloon catheter is 30 required to assist expansion during delivery. The disadvantages of this design include lack of -8sufficient anchoring mechanism; problematic interference concerns with adjacent tissues and anatomical structures; fatigue concecms associated with the multiplicity of segments, connections and sutures; lack of an adequately controlled and biased flow-regulation mechanism; uncertain effective valve orifice, difficult manufacture; balloon dilation requirement; complex, difficult and inaccurate delivery and large delivery profile. The Besseler valve discloses methods and devices for the endovascular removal of a defective heart valve and the replacement with a percutaneous cardiac valve. The device is comprised of a self-expanding stent member with a flexible valve disposed within. The sten. member is of a self-expanding cylindrical shape made from a closed wire in formed in a zigzag configuration that can be a single piece, stamped or extruded or formed by welding 10 the free ends together. The flow-regulation mechanism is comprised of an arcuate portion which contains a slit (or slits) to fonn leaflets and a cuff portion which is sutured to and encloses the stent. The preferred flow regulator is a porcine pericardium with three cusps. An additional flow regulator is described in which the graft material that comprises the leaflets (no additional mechanisms for flow-regulation) extends to form the outer cuff portion and is 15 attached to the stent portion with sutures. The anchoring segment is provided by a plurality of barbs carried by the stent (and therefor penetrating the cuff-graft segment). Delivery requires endoluminal removal of the natural valve because the barb anchors will malfunction if they are orthotopically secured to the native leaflets instead of the more rigid tissue at die native annulus or vessel wall Delivery involves a catheter within which the device and a pusher 20 rod are disposed. The disadvantages of the device are lack of a well defined and biased flow regulation mechanism, anatomic valve removal is required thereby lengthening the procedure time, increasing difficulty and reducing clinical practicality, trauma-inducing barbs as described above and the device is unstable and prone to migration if barbs are omitted. The Khosravi valve discloses a percutaneous prosthetic valve comprised of a coiled 25 sheet stent similar to that described by Derbyshire, U.S. Pat. No. 5,007,926, to which a plurality of flaps are mounted on the interior surface to form a flow-regulation mechanism that may be comprised of a biocampatible material. The disadvantages of this design include problematic interactions between the stent and flaps in the delivery state, lack of clinical data on coiled stent performance, the lack of a detailed mechanism to ensure that the flaps will -9create a competent one-directional valve, lack of appropriate anchoring means, and the design requirements imposed by surrounding anatomical structures are ignored. The Zadno-Azizi valve discloses a device in which flow-regulation is provided by a flap disposed within a frame structure capable of taking an insertion state and an expanded state. The preferred embodiment of the flow-regulation mechanism is defined by a 5 longitudinal valve body made of a sufficiently resilient material with a sli(s) that extends longitudinally through the valve body. Increased sub-valvular pressure is said to cause the valve body to expand thereby opening the slit and allowing fluid flow (here through. The valve body extends into the into the lumen of the body passage such that increased supra valvular pressure will prevent the slit front opening thereby effecting one-directional flow. 10 The device includes embedding the frame within the seal or graft material through injection molding, blow molding and insertion molding. The disadvantages of the device include the flow-regulation mechanism provides a small effective valve orifice, the turbidity caused by the multiple slit mechanisms, the large delivery profile required by the disclosed embodiments and the lack of acute anchoring means. i5 Finally, the Leonhardt valve is comprised of a tubular graft having radially compressible annular spring portions and a flow regulator, which is preferably a biological valve disposed within. In addition to oversizing the spring stent by 30/6, anchoring means is provided by a light-activated biocompatible tissue adhesive is located on the outside of the tubular graft and seals to the living tissue. The stent section is comprised ofra single piece of 20 superelastic wire formed into a zigzag shape and connected together by crimping tubes, adhesives or welds. A malleable thin-walled, biocompatible, flexible, expandable, woven fabric graft material is connected to the outside of the stent that is in turn connected to the biological flow regulator. Disadvantages of this device include those profile concerns associated with biological valves and unsupported graft-leaflet regulators, a large diameter 25 complex delivery system and method which requires multiple anchoring balloons and the use of a light activated tissue adhesive in addition to any prior valvuloplasty performed, interference with surrounding anatomy and the questionable clinical utility and feasibility of the light actuated anchoring means. As used herein the term "Graft" is intended to indicate any type of tubular member which exhibits integral columnar and circumferential strength 30 and which has openings which pass through the thickness of thc tubular member -10- In accordance with a preferred embodiment of the invention, a graft member is formed as a discrete thin sheet or tubc of biocompatible metal and/or pseudometal. A plurality of openings is provided which pass transverscly through the graft member. The plurality of openings may be random or may be patlrned. ft is preferable that the size of 5 each of the plurality of openings be such as to permit cellular migration through each opening, without permitting fluid flow there through. In this manner, blood cannot flow through the plurality of openings, but various cells or proteins may freely pass through the plurality of openings to promote graft healing in vivo. In accordance with another aspect of the inventive graft embodiment, it is contemplated that two graft members are employed, 10 with an outer diameter of a first graft member being smaller than the inner diameter of a second graft member, such that the first graft member is concentrically engageable within a lumen of the second graft member. Both the first and second graft member have a pattern of a plurality of openings passing there through. The first and second graft members are positioned concentrically with respect to one another, with the plurality of patterned openings 15 being positioned out of phase relative to one another such as to create a tortuous cellular migration pathway through the wall of the concentrically engaged first and second graft members. In order to facilitate cellular migration through and healing of the first and second graft members in vivo. it is preferable to provide additional cellular migration pathways that communicate between the plurality of openings in the first and second graft members. These 20 additional cellular migration pathways may be imparted as 1) a plurality of projections fonned on either the luminal surface of the second graft or the abluminal surface of the first graft, or both, which serve as spacers and act to maintain an annular opening between the first and second graft members that permits cellular migration and cellular communication between the plurality of openings in the first and second graft members, or 2) a plurality of 25 microgrooves, which may be random, radial, helical, or longitudinal relative to the longitudinal axis of the first and second graft members, the plurality of microgrooves being of a sufficient size to permit cellular migration and propagation along the groove without permitting fluid flow there through, the microgrooves serve as cellular migration conduits between the plurality of openings in the first and second graft members. -11- In order to improve healing response, it is preferable that the materials employed have substantially homogenous surface profiles at the blood or tissue contact surfaces thereof. A substantiaUy homogeneous surface profile is achieved by controlling heterogeneities along the blood or tissue-contacting surface of the material. The heterogeneities that are controlled in accordance with an embodiment of the present invention include: grain size, grain phase, 5 grain material composition, stent-material composition, and surface topography at the blood flow surface ofthestent. Additionally, the present invention provides methods of making endolurninal devices having controlled beterogeneities in the device material along the blood flow or tissue-contacting surface of the device. Material heterogeneities are preferably controlled by using conventional methods of vacuum deposition of materials onto a substrate. 10 The surface of a solid, homogeneous material can be conceptualized as having unsaturated inter-atomic and internolecular bonds fonning a reactive plane ready to interact. with the environment [n practice, a perfectly clean surface is unattainable because of immediate adsorption of airborne species, upon exposure to ambient air, of 0, 0,, CO 2 , SO,. NO, hydrocarbons and other more complex reactive molecules. Reaction with oxygen 15 implies the formation of oxides on a metal surface, a self-limiting process, known as passivation. An oxidized surface is also reactive with air, by adsorbing simple, organic airborne compounds. Assuming the existence of bulk material of homogeneous subsurface and surface composition, oxygen and hydrocarbons may adsorb homogeneously. Therefore, further exposure to another environment, such as the vascular compartment, may be followed 20 by a uniform biological response. Current metallic vascular devices, such as stents, are made from bulk metals made by conventional methods which employ many steps that introduce processing aides to the metals make stent precursors, such as hypotubes. For example, olefins trapped by cold drawing and transformed into carbides or elemental carbon deposit by heat treatment, typically yield large 25 carbon rich areas in 316L stainless steel tubing manufactured by cold drawing process. The conventional stents have marked surface and subsurface heterogeneity resulting from manufacturing processes (friction material transfer from tooling, inclusion of lubricants, chemical segregation from heat treatments). This results in formation of surface and subsurface inclusions with chemical composition and, therefore, reactivity different from the 30 bulk material. Oxidation, organic contamination, water and electrolytic interaction, protein -12.

adsorption and cellular interaction may, therefore, be altered on the surface of such inclusion spots. Unpredictable distributions of inclusions such as those mentioned above provide unpredictable and uncontrolled heterogeneous surface available for interaction with plasma proteins and cells. Specifically, these inclusions interrupt the regular distribution pattern of surface free energy and electrostatic charges on the metal surface that determine the nature 5 and extent. of plasma protein interaction. Plasma proteins deposit nonspecifically on. surfaces according to their relative affinity for polar or non-polar areas and their concentration in blood. A replacement process known as the Vroman effect, Vroman L., The importance of surfaces in contact base reactions, Seminars of Thrombosis and Hemostasis 1987; 13(1): 79 85, determines a Litie-dependent sequential replacement of predominant proteins at an 10 artificial surflice, starting with albumin, following with IgG, fibrinogen and ending with high molecular weight kininogen. Despite this variability in surface adsorption specificity, some of the adsorbed proteins have rceptors available for cell attachment and therefore constitute adhesive sites. Examples arc: fibrinogen glycoprotein receptor lIb~la for platelets and fibronectin RGD sequence for many blood activated cells. Since the coverage of an artificial 15 surface with cudothelial cells is a favorable end-point in the healing process, favoring endotlieliaization in device design is desirable in implantable vascular device manufacturing. Normally, endothelial cells (EC) migrate and proliferate to cover denuded areas until confluence is achieved. Migration, quantitatively more important than proliferation, proceeds under nonnal blood flow roughly at a rate of25 im/hr or 2.5 times the diameter of an EC, 20 which is nominally I OpLm. BC migrate by a rolling motion of the cell membrane, coordinated by a complex system of intracellular filaments attached to clusters of cell membrane integrin receptors, specifically focal contact points. The integrins within the focal contact sites are expressed according to complex signaling mechanisms and eventually couple to specific amino acid sequences in substrate adhesion molecules (such as RGD, mentioned above). An 25 EC has roughly 16-22% of its cell surface represented by integrin clusters. Davics, P.F., Robotewskyi A., Griem M.L. Endothelial cell adhesion in real time. J. Clin.nveslt. 1993; 91:2640-2652, Davies, PF.. Robotewski, A., Gricm, M.L., Oualitiative studies of endothelial cell adhesion. J'Clin.nvest.1994: 93:2031-2038. This is a dynamic process, which implies more than 50% remodeling in 30 minutes. The focal adhesion contacts vary in size and 30 disbibution, but 80% of them measure less than 6 pm-. with the majority of them being about -13- I m and tend to elongate in the direction of flow and concentrate at leading edges of the cell. Although the process of recognition and signaling to determine specific attachment receptor response to attachment sites is incompletely understood, regular availability of attachment sites, more likely than not, would favorably influence attachment and migration. Irregular or unpredictable distribution of attachment sites, that might occur as a result of 5 various inclusions, with spacing equal or smaller to one whole cell length, is likely to determine alternating hostile and favorable attachment conditions along the path of a migrating cell. These conditions may vary from optimal attachment force and migration speed to insufficient holding strength to sustain attachment, resulting in cell slough under arterial flow conditions. Due to present manufacturing processes, current implantable 10 vascular devices exhibit such variability in surface composition as determined by surface sensitive techniques such as atomic force microscopy, X-ray photoelectron spectroscopy and time-o f[flight secondary ion mass spectroscopy. There have been numerous attempts to increase endothelialization of implanted stents, including covering the stent with a polymeric material (U.S. Patent No. 5,897,911), 15 imparting a diamond-like carbon coating onto the stent (U.S. Patent No. 5,725,573), covalently binding hydrophobic moieties to a heparin molecule (U.S. Patent No. 5,955.588), coating a stent with a layer of blue to black zirconium oxide or zirconium nitride (U.S. Patent No. 5,649,951), coating a stent with a layer of turbostratic carbon (U.S. Patent No. 5,387,247), coating the tissue-ontacting surface of a stent with a thin layer of a Group VB 20 metal (U.S. Patent No. 5,607,463), imparting a porous coating of titanium or of a titanium alloy, such as Ti-Nb-Zr alloy, onto the surface of a stent (U.S. Patent No. 5,690,670), coating the stent, under ultrasonic conditions, with a synthetic or biological, active or inactive agent, such as heparin, endothelium derived growth factor, vascular growth factors, silicone, polyurethane, or polytetrafluoroethylene, U.S. Patent No. 5,891,507), coating a stent with a 25 silane compound with vinyl functionality, then forming a graft polymer by polymerization with the vinyl groups of the silane compound (U.S. Patent No. 5,782,908), grafting monomers, oligomers or polymers onto the surface of a stent using infrared radiation, microwave radiation or high voltage polymerization to impart the property of the monomer, oligomer or polymcr to the stent (U.S. Patent No. 5,932,299). -14- Thus, the problems of thrombogenicity and re-cndothelialization associated with stents havc been addressed by thc art in various manners which cover the stent with either a biologically active or an inactive covering which is less thmmbogenic than the stent material and/or which has an increased capacity for promoting re-endothelialization of the stent situs. These solutions, however, all require the use of existing stents as substrates for surface 5 derivatization or modification, and each of the solutions result in a biased or laminate stricture huilt upon the stent substrate. These prior art coated stents are susceptible to delaminating and/or cracking of the coating when mechanical stresses of transluminal catheter delivery and/or radial expansion in vivo. Moreover, because these prior art stents employ coatings applied to stents fabricated in accordance with conventional stent formation 10 techniques, e.g., cold-forming metals, the underlying stent substrate is characterized by uncontrolled heterogeneities on the surface thereof, Thus, coatings merely are laid upon the heterogeneous scent surface, and inherently conform to the topographical heterogeneities in the stent surface and mirror these heterogeneities at the blood contact surface of the resulting coating. This is conceptually similar to adding a coat of fresh paint over an old coating of 5 blistered paint; the fresh coating will conform to the blistering and eventually, blister and delaminate from the underlying substrate. Thus, topographical heterogeneities are typically telegraphed through a surface coating. Chemical heterogeneities, on the other hand, may not be telegraphed through a surface coating but may be exposed due to cracking or peeling of the adherent layer, depending upon the particular chemical heterogeneity. 20 The current invention entails creating valve flap members and other implantable septa, for example, access ports, of vacuum deposited metal and/or pseudometallic materials. According to a preferred embodiment of the invention, the manufacture of valve flap members and other implantable septa fabricated of metallic and/or pseudometallic films is controlled to attain a regular, homogeneous atomic and molecular pattern of distribution 25 along their fluid-contacting surfaces. This avoids the marked variations in surface composition, creating predictable oxidation and organic adsorption patterns and has predictable interactions with water, electrolytes, proteins and cells. Particularly, EC migration is supported by a homogeneous distribution of binding domains that serve as natural or implanted cell attachment sites, in order to promote unimpeded migration and 30 attachment. Based on observed EC attachment mechanisms such binding domains should -15have a repeating pattern along the blood contact surface of no less than 1 pm radius and 2 pim border-to-border spacing between binding domains. Ideally, the inter-binding domain spacing is less than the nominal diameter of an endothelial cell in order to ensure that at any given time, a portion of an endothelial cell is in proximity to a binding domain. Summary of the Invention 5 In accordance with the present invention, there is provided an improved film structure for implantable moveable septa, such as valve flaps, access ports, prosthetic ventricular members or similar types of anatomical prosthetic replacements. It is, therefore, a primary of the present invention to provide a prosthetic unidirectional valve having valve flap members fabricated of biocompatible metal and/or 10 pseudometallic films. The valvular prosthesis of the present invention consists generally of a stent body member, a graft, and valve flaps. The stent body member may be fashioned by laser cutting a hypotube or by weaving wires into a tubular structure, and is preferably made from shape memory or super-elastic materials, such as nickel-titanium alloys known as NITINOL, but may be made of balloon expandable stainless steel or other plastically 15 deformable stent materials as are known in the art, such as titanium or tantalum, or may be self-expanding such as by weaving stainless steel wire into a stressed-tubular configuration in order to impart elastic strain to the wire. The graft is preferably a biocompatible, fatigue resistant membrane which is capable of endothelialization, and is attached to the stent body member on at least portions of either or both the luminal and abluminal surfaces of the stent 20 body member by suturing to or encapsulating stent struts. The valve leaflets are preferably formed by sections of the graft material attached to the stent body member. The stent body member is shaped to include the following stent sections: proximal and distal anchors, a intermediate annular stent section, and at least one valve arm or blood flow regulator struts. The proximal and distal anchor sections are present at opposing ends of 25 the prosthesis and subtend either an acute, right or obtuse angle with a central longitudinal axis that defines the cylindrical prosthesis. In either the CV or CC configurations, the proximal anchor is configured to assume approximately a right angle radiating outward from the central longitudinal axis of the prosthesis in a manner which provides an anchoring fange. When being delivered from a delivery catheter, the proximal anchor is deployed first -16and engages the native tissue and anatomical structures just proximal to thc anatomic valve, such as the left ventricle wall in the case of retrograde orthotopic delivery at the aortic valve. Deployment of the proximal anchor permits the intermediate annular stent section to be deployed an reside within the native valve annular space and the abluninal surface of the intermediate annular stent section to abut and outwardly radially compress the anatomic 5 valve leaflets against the vascular wall. The distal anchor is then deployed and radially expands to contact the vascular wall and retain the prosthesis in position, thereby excluding the anatomic valve leaflets from the bloodflow and replacing them with the prosthetic valve leaflets. Flow regulation in the inventive stent valve prosthesis is provided by the combination of the prosthetic valve leaflets and the valve arms and is biased closed in a manner similar manner to that described for a surgically implanted replacement heart valve by Boretos, U.S. Pat. No. 4,222,126. The valve regulator-struts are preferably configured to be positioned to 5 radiate inward from the stent body member toward the central longitudinal axis of the prosthesis, The graft-leaflet has the appearance of a partially-everted tube where the innermost layer, on the luminal surface of the stent body member, forms the leaflets and the outer-most layer, on the abluminal surface of the stent body member, forms a sealing graft which contacts and excludes the immobilized anatomical valve leaflets. The struts of the 10 stent are encapsulated by the outer graft-membrane. The valve regulator-struts are encapsulated by the inner leaflet-membrane and serve to bias the valve to the closed position. The regulator-struts also prevent inversion or prolapse of the otherwise unsupported leaflet membrane during increased supra-valvular pressure. The inner leaflet-membrane may also be attached to the outer graft-membrane at points equidistant from the valve strut-arms in a 15 manner analogous to that described for a surgically implanted replacement heart valve by Cox, U.S. Pat. No. 5,824,063. The combination of the thin walled properties of the leaflet membrane, the one-sided open lumen support of the intermediate annular stent section, the free ends of the valve leaflets, the biasing and support provided by the valve regulator-struts and the attachment points all work to provide a prosthetic valvular device capable of 20 endoluminal delivery which simulates the hemodynamic properties of a healthy anatomical cardiac or venous valve. -17- - 18 In accordance with another embodiment of the invention, there is provided an implantable valvular prosthesis having a graft covering and valve flap members that are each formed as discrete laminated films of a biocompatible metal or pseudometal. A plurality of openings is provided which pass transversely through the graft member. The 5 plurality of openings may be random or may be patterned. It is preferable that the size of each of the plurality of openings be such as to permit cellular migration through each opening, without permitting fluid flow there through. In this manner, blood cannot flow through the plurality of openings, but various cells or proteins may freely pass through the plurality of openings to promote graft healing in vivo. to Finally, in accordance with a further aspect of the present invention, there is provided an implantable valvular prosthesis having valve flap members and a covering graft member that are fabricated from metallic and/or pseudomctallic films that present a blood or tissue contact surface that is substantially homogeneous in material constitution. 15 Brief Description of Figures FIG. I is a perspective view of the inventive valve stent chamber-to-vessel embodiment in its fully deployed state. FIG. 2 is a perspective view of the inventive valve stent chamber-to-vessel 20 embodiment in its fully deployed state with the outermost graft layer and stent layer partially removed to show an embodiment of the valve apparatus. FIG. 3 is a top view of the inventive valve stent chamber-to-vessel embodiment in its fully deployed state. FIG. 4 shows the cross-section taken along line 4-4 of FIG. 1. 25 FIG. 5 is a bottom view of the inventive valve stent chamber-to-vessel embodiment in its fully deployed state. FIG. 6A illustrates a cross-sectional view of a human heart during systole with the inventive valve stent chamber-to-vessel embodiment implanted in the aortic valve and illustrating a blood flow vector of an ejection fraction leaving the left ventricle and 30 passing through the inventive valve stent. FIG. 6B illustrates a cross-sectional view of a human heart during diastole with the inventive valve stent chamber-to-vessel embodiment implanted in the aortic valve and illustrating a blood flow vector of blood passing from the left atrium, through the mitral valve and into the left ventricle during and a retrograde blood flow vector blocked by the inventive valve stent in the aorta. FIG. 7 is a perspective view of the inventive valve stent chamber-to-chamber 5 embodiment in its fully deployed state. FIG. 8 is a is a perspective view of the inventive valve stei chamber-to-chamber embodiment in its fully deployed state with the outermost grain layer and stent layer partially removed to show an embodiment of the valve apparatus. FIG. 9 is a top view of the inventive valve stent chamber-to-chamber embodiment in 10 its fully deployed state. FIG. 10 shows the cross sectional view taken along line 10-10 of FIG. 7. FIG. I I is a bottom view of inventive valve stent chanber-to-chamber embodiment in its fully deployed state. FIG. 12A illustrates a cross-sectional view of a human heart during atrial systole IS with the inventive valve stent chaniber-to-chamber emhodimenn implited at the site of the mitral valve and illustrating a blood flow vector of a filing fraction leaving the left atrium and entering the left ventricle. FIG. 12B illustrates a cross-sectional view of a human heart during atrial diastole with the inventive valve stent chamber-to-chamber embodiment implanted at the site of the 20 mitral valve and illustrating a blood flow vector of an ejection fraction from the left ventricle to the aorta and the back pressure against the implanted mitral valve prosthesis. FIG. 13 is a perspective view of the chamber-to-vessel configuration in the fully deployed state. FIG. 14 is a perspective view of the same configuration in the fully deployed state 25 with the outermost graft layer and stent layer partially removed to show an embodiment of the valve apparatus. FIG. 15 is a top view of the same configuration. FIG. 16 shows the cross sectional view of the same con figuration for the deployed state. 30 FIG. 17 is a bottom view of the same configuration. -19- FIG. 18A and 18B show cross-sectional views of a vein and venous valve illustrating the inventive prosthetic venous valve in the open and closed state. FIG. 19 is a cross-sectional diagrammatic view of a valvuloplasty and stent valve delivery catheter in accordance with the present invention. 5 FIGS. 20A-201 are diagrammatic cross-sectional views illustrating single catheter valvuloplasty, inventive stent valve delivery and stent valve operation in situ in accordance with the method of the present invention. Detailed Description of the Preferred Embodiments 10 The present invention consists generally of three preferred embodiments, cach embodiment corresponding to a prosthetic stent valve configuration adapted for either heart chamber to blood vessel communication, chamber to chamber communication or vessel to vessel, or intravascular configuration. Certain elements are common to each of the preferred embodiments of the invention, specifically, each embodiment includes a stent body member 15 which defines a central annular opening along the longitudinal axis of the stent body member, a graft member which covers at least a portion of the stent body member along either the luninal or abluminal surfaces of the stent body member, at least one biasing arm is provided and projects from the stent body member and into the central annular opening of the stent body member, and at least one valve flap member which is coupled to each biasing arm 20 such that the biasing arm biases the valve flap member to occlude the central annular opening of the stent body member under conditions of a zero pressure. differential across the prosthesis. The stent body member is preferably made of a shape memory material or superelastic material, such as NITINOL, but also is fabricated from either plastically deformable materials or spring-elastic materials such as are well known in the art. 25 Additionally, the stent body member has three main operable sections, a proximal anchor section, a distal anchor section and an intermediate annular section which is intermediate the proximal and distal anchor sections. Depending upon the specific inventive embodiment, the distal and proximal anchor sections may be either a diametrically enlarged section or may be a flanged section. The intermediate annular section defines a valve exclusion region and 30 primary blood flow channel of the inventive valve stent The intermediate annular section defines a luminal opening through which blood flow is established. The ti-ansverse crois -20section of the luminal opening may be circular, elliptical, ovular, triangular or quadralincar, depending upon the specific application for which the valve stent is being employed. Thus, for example, where a tricuspid valve is particularly stenosed, it may be preferable to employ a valve stent with a luminal opening in the intermiediate annular section which has a 5 triangular transverse cross-sectional dimension. In each of the foregoing embodiments, the graft member and the valve flap mcmbcrs are fabricated of a biocompatible metal and/or a biocompatible pseudometal and arc formed as films of material that are preferably laminated to enhance their material properties. The metal fihns may be micro or nanoporous to enhance endothelialization as described in greater 10 detail in parent patent application U.S. Serial No. 09/853,985 filed May 11, 2001, which is hereby incorporated by reference. Suitable materials to fabricated the inventive graft and valve flap members are chosen for their biocompatibility. mechanical properties, i.e., tensile strength, yield strength, and their ese of deposition include, without limitation, the following: titanium, vanadium, aluminum, nickel, tantalum, zirconium, chromium, silver, 15 gold, silicon, magnesium, niobium, scandium, platinum, cobalt, palladium, mangancsc, molybdenum and alloys thereof, such as zirconium-titanium-tantalum alloys, nitinol. and stainless steel. The graft member and the valve flap members are foned by vacuum deposition methodologies. Chamber-to. Vessel Configuration 20 An implantable prosthesis or prosthetic valve in accordance with certain embodiments of the chamber-to-vessel CV configuration of the present invention is illustrated generally in Figures 1-5. The chamber-to-vessel valve stent 10 consists of an expandable stont body members 2 and graft member 11. 'e stent body member 12 is 25 preferably made from a shape memory and/or superelastic NITINOL material, or thermomechanically similar materials, but may be made of plastically defonnable or elastically compliant materials such as stainless steel, titanium or tantalum. The graft member II is fabricated of biocompatible metal and/or pscudometallic materials, such as thin film stainless steel, nickel-titanium alloy, tantalum, titanium or carbon fibcr. The stent body 30 member 12 is configured to have three fiinctional sections: a proximal anchor flange 22, an intermediate annular section 20 and a distal anchor section 16. The stein body member 12.

as with conventional stents is formed of a plurality of stent struts 13 which define interstices 14 between adjacent stent struts 13. The stent body member preferably also includes a transitional section IS that interconnects the intermediate annular section 20 and the distal anchor section 16, which together define a valve exclusion region of the inventive stent v'ah-e 5 10 to exclude the anatomic valve after implantation. The proximal anchor flange 22, the intermediate annular section 20 and the distal. anchor section 16 arc each formed during the formation of the stent body member and are formed from the same material as the stent body member and comprise stent struts 13 and intervening interstices 14 between adjacent pairs of stent siruts 13. The anchor flange 22, for example, consists of a plurality ofstent siruts and a 10 plurality of stent interstices, which project radially outwardly away from the central longitudinal axis of the stent body member. Thus, the different sections of the stent body member 12 are defined by the positional oricatation of the stent struts and interstices relative to the central longitudinal axis of the stent body member 12. With reference to FIG. 2, there is shown in greater detail the valve body 26 and valve 15 arms or flow regulator struts 24 coupled to the stent body member L2. The valve body 26 subtends the central annular opening of the stent valve 10 and is illustrated in its closed position. In accordance with one embodiment of the present invention, the graft member 11 consists of an outer or abluminal graft member I a and an inner or luminal graft member 1lb. The outer graft member I la encloses at least a portion of the ablurninal surface of the 20 intermediate annular section 20 of the stent body member, while the inner graft member I lb is coupled, on the luminal surface of the intermediate annular section 20 of the stent body member 12, to the outer graft member I la through the interstices 14 of the stent body member. The valve body 26 is formed by everting the inner graft member LI b toward the central longitudinal axis of the stent body member 12 such that free ends or valve flap 25 portions 28 of the inner graft member Ib are oriented toward the distal anchor section 16 of the stent body member 12 and a pocket or envelope 27 is formed at the eversion point of the inner graft member I I b adjacent the junction between the intermediate annular section 20 and the proximal anchor flange 22 of the stent body member 12. Alternatively, portions of the outer graft member I Ia may be passed through to the luminal surface of the stent body 30 member 12, thereby becoming the inner graft member 1 lb and everted to form the valve body 26. -22- Valve arms or regulator struts 24 are coupled or formed integral with the stent body member 12 and are positioned adjacent the junction point between intermediate annular section 20 and the proximal anchor flange 22 of the stent body member 12. The valve arms 24 are oriented radially inward toward the central longitudinal axis of the stent body member 5 12 when in their zero strain state. The valve anns 24 are attached or coupled to the valve flap portions 28 of the inner graft member leaflets to bias the valve flap portions 28 to the closed position when under zero pressure differential across the stent valve 10. The zero strain position of the valve arms 24 is radially inward and orthogonal to the central longitudinal axis of the stent valve 10. Valve arms 24 have a length which is 10 preferably longer than the radius of the luninal diameter of the stent valve 10, and they extent distally into the lumen of the stent valve 10 such that, in conjunction with the action of the valve leaflets 28, the valve arms 24 are prevented from achieving their zero strain configuration thereby biasing the valve closed. As shown in FIG. 4, the valve arms 24 force the valve leaflets 28 to collapse into the center of the lumen of the stent valve 10, thus 15 biasing the valve to its closed position. It is preferable to couple sections of the valve flaps 28, along a longitudinal seam 29, to the inner graft member [lb and the outer graft member 11 a at points equidistant from the valve arms 24 in order to impart a more cusp-like structure to the valve flaps 28. R should be appreciated, that the graft member 11 should cover at least a portion of the abluminal 20 surface of the stent body member 12 in order to exclude the anatomic valves, but may also cover portions or all of the stent valve member 12. including the distal anchor section 16, the intermediate annular section 20, the transition section 18 and/or the proximal anchor flange 22, on either or both of the luminal and abluminal surfaces of the stent body member. In accordance with a particularly prefed embodiment of the CV valve start 10, the 25 proximal anchor flange 22, which consists of a plurality of stent struts and stent interstices which project radially outward away from the central longitudinal axis of the valve stent 10, is configured to have one or more stent struts eliminated from the proximal anchor flange 22 to define an open region which is positioned in such a manner as to prevent the CV valve stent 10 from interfering with or impinging upon an adjacent anatomic structure. For 30 example, where the CV valve stent 10 is to be an aortic valve prosthesis, it is known that the mitral valve is immediately adjacent the aortic valve, and the mitral valve flaps deflect -23toward the lefi ventricle. Thus, placing the CV valve stent 10 such that the proximal anchor flange 22 is adjacent the mitral valve might, depending upon the particular patient anatomy, interfere with normal opening of the mitral valve flaps. By eliminating one or more of the stent struts in the proximal anchor flange 22, an opening is created which permits the mitral 5 valve flaps to deflect ventricularly without impinging upon the proximal anchor flange 22 of the CV valve stent 10. Similarly, the stent struts of the CV valve stent 10 may be oriented in such a manner as to create interstices of greater or smaller area between adjacent struts, to accorrunodate a particular patient anatomy. For example, where the stent struts in the distal anchor section 16 10 would overly an artery branching from the aorta, such as the coronary ostreum arteries, it may be desirable to either eliminate certain sten struts, or to configure certain stent struts to define a greater interstitial area to accommodate greater blood flow into the coronary ostreun. In the case of providing an oriented opening in the proximal anchor flange, or an 15 oriented opening in the interstitial spaces of the distal anchor, it is desirable to provide radiopaque markers on the stent body member 12 to permit the CV valve stent to be oriented correctly relative to the anatomic structures. Figures 6A and 6B illustrate the inventive CV stent valve 10 implanted in the position of the aortic valve and excluding the anatomic aortic valve AV. FIG. 6A illustrates the heart 20 during systole in which a positive pressure is applied to the prosthetic aortic valve by contraction of the left ventricle LV and the ejection fraction represented by the arrow. The systolic pressure overcomes the bias exerted by the valve arms 24 and causes the valve leaflets 26 to open and release the ejection fraction into the aorta. FIG. 6 B illustrates that the presence of a negative pressure head across the stent valve 10, i.e. such as that during 25 diastole, causes the biased valve leaflets 26 which are already closed, to further close, and prevent regurgitation from the aorta into the left ventricle. Chamber-to- Chamber Configuration Figures 7-11 illustrate the inventive stent valve in the chamber-to-chamber (CC) 30 configuration 40. The CC valve stent 40 is constructed in a manner which is virtually identical to that of the CV valve stent 10 described above, except that the distal anchor -24section 16 of the CV valve stent 10 is not present in the CC valve stent 40, but is substituted by a distal anchor flange 42 in the CC stent valve. Thus, like the CV valve stent 10, described above, the CC valve stent 40 if formed of a stent body member 12 and a grafl member 11, with the graft member having luminal 1 lb and abluminal Ila portions which 5 cover at least portions of the luminal and abluminal surfaces of the stent body member 12, respectively. The CC valve stent 40 has both a proximal anchor flange 44 and a distal anchor flange 42 which are formed of sections of the stent body member 12 which project radially outward away fronm the central longitudinal axis of the CC valve stent 40 at opposing ends of the stent body member 12. 10 Like the CV valve stent 10, the luminal graft portion 1lb is everted inwardly toward the central longitudinal axis of the valve stent 40 and free ends 28 of the luminal grail portion I lb to form valve flaps 26 which project distally toward distal anchor flange 42. Flow regulation struts 24 are coupled to or integral with the proximal anchor flange 44 and intennediate annular section 20 and project radially inward toward the central longitudinal 15 axis of the CC valve stent 40. The valve flaps 26 are coupled to the flow regulation struts 24 and the flow regulation struts 24 bias the valve flaps 26 to a closed position under a zero strain load. Like with the CV stent valve 10, it is preferable to couple sections of the valve flaps 28, along a longitudinal seam 29, to the inner graft member I lb and the outer graft member 20 II a at points equidistant from the valve arms 24 in order to impart a more cusp-like structure to the valve flaps 28. Turning to Figures 12A and B there is illustrated the inventive CC stent valve 40 implanted in the position of the mitral valve and excluding the anatomic mitral valve MV. FIG. 12A illustrates the heart during atrial systole in which a positive pressure is applied to 25 the prosthetic mitral valve by contraction of the left atrium LA and the pressure exerted by the blood flow represented by the arrow. The atrial systolic pressure overcomes the bias exerted by the valve arms 24 onto the valve leaflets 26, and causes the valve leaflets 26 to open and release the atrial ejection fraction into the left ventricle. FIG. 12 B illustrates that the presence of a negative pressure head across the stent valve 40, L.e. such as that during 30 atrial diastole, causes the biased valve leaflets 26 which are already closed, to further close, and prevent backflow from the left ventricle into the left atrium. -25- In accordance with another preferred embodiment of the invention, the CC configuration may be adapted for use in repairing septal defects. By simply substituting a membrane for the valve leaflets 26, the lumen of the stent body member 12 is occluded. The CC stent valve 40 may be delivered endoluminally and placed into a position to subtend a 5 septal defect and deployed to occlude the septal defect. Vessel-o- Jessel Configuration Turning nowv to Figures 13-17, there is illustrated the inventive stent valve in its vessel-to-vessel (VV) valve stent configuration 50. The VV valve stent 50 is constructed in 10 a manner which is virtually identical to that of the CV valve stent 10 described above, except that the proximal anchor flange 22 of the CV valve stcnt 10 is not present in the VV valve stent 50, but is substituted by a proximal anchor section 52 in the VV stent valve. 'Thus, like the CV valve stent 10, described above, the VV valve stent 50 is formed of a. stent body member 12 and a graft member I1, with the graft member having luminal I lb and abluminal I I a portions which cover at least portions of the luminal and abluminal surfaces of the stent body member 12, respectively. The VV valve stent 50 has both a proximal anchor section 52 and a distal anchor section 54 which are formed of sections of the stent body member 12 which are diametrically greater than the intermediate annular section 20 of the VV valve stent 50. Transition sections 56 and 58 taper outwardly away from the central longitudinal 20 axis of the VV valve stent 50 and interconnect the intermediate annular section 20 to each of the distal anchor section 54 and the proximal anchor section 52, respectively. Like the CV valve stent 10. in the VV valve stent 50, the graft member 11, particularly the luminal graft portion I lb or the abluminal graft portion I a, or both, is everted inwardly toward the central longitudinal axis of the valve stent 40 and free ends 28 of 25 the luminal graft portion 1 lb to form valve flaps 26 which project distally toward distal anchor flange 42. Flow regulation struts 24 are coupled to or integral with the stent body member at the proximal transition section 58 and project radially inward toward the central longitudinal axis of the VV valve stent 50. The valve flaps 26 are coupled to the flow regulation struts 24 and the flow regulation struts 24 bias the valve flaps 26 to a closed 30 position under a zero strain load. Like with the CV stem valve 10 and the CC stent valve 40, it is preferable to couple sections of the valve flaps 28, along a longitudinal seam 29, to the -26inner graft member I lb and the outer graft member I la at points equidistant from the valve arms 24 in order to impart a more cusp-like structure to the valve flaps 28. Turning to Figures 18A and B there is illustrated the inventive VV stent valve 50 implanted in the position of a venous valve and excluding the anatomic venous valve flaps 5 VE. FIG. I 8A illustrates the vein under systolic blood pressure in which a positive pressure is applied to the prosthetic venous valve and the pressure exerted by the blood flow represented by the arrow. The sysiolic pressure overcomes the bias exerted by the valve arms 24 onto the valve leaflets 26, and causes the valve leaflets 26 to open and permit blood flow through the prosthesis. FIG. 18 B illustrates that the presence of a negative pressure 10 head across the VV stent valve 50, i.e. such as which exists at physiological diastolic pressures, causes the biased valve leaflets 26 which are already closed, to further close, and prevent backflow from the left ventricle into the left atrium. The purpose of the proximal 54 and distal 52 anchor sections of the stent body member 12 is to anchor the prosthesis at the anatomic vessel-vessel junction, such as a 15 venous valve, while causing minimal interference with adjacent tissue. The intermediate annular section 20 of the VV stent valve 50 excludes diseased anatomic leaflets and surrounding tissue froin the Dow field. The flare angle of the transition sections 56, 58 between the intermediate annular section 20 and each of the proximal and distal anchor sections 54, 52, respectively, may be an acute angle, a right angle or an obtuse angle, 20 depending upon the anatomical physiological requirements of the implantation site. Alternatively, the transition sections 56, 58 may be coplanar with the proximal and distal anchor section 52, 54, respectively, thereby, eliminating any transition flare angle, depending upon the anatomical and physiological requirements of the delivery site. 25 Single Catheter Valvuloplasty Slent Valve Del iery System and MetAod of Delivery In accordance with the present invention, there is also provide a single catheter valvuloplasty and valve stent delivery system 200 illustrated in FIG. 19. The objective of the single catheter delivery system 200 is to permit the surgeon or interventionalist to percutaneously deliver and deploy the inventive valve stent 10, 40 or 50 at the desired 30 anatomical site and to perform valvuloplasty with a single catheter. In accordance with the preferred embodiment of the single catheter delivery system 200 of the present invention, -27there is provided a catheter body210 having dual lumens212, 216. A first lumen 212 is provided as a guidewire lumen and is defined by a guidewire shaft 222 that traverses the length of the catheter body 210. A second lumen is an inflation lumen 216 for communicating an inflation fluid, such as saline, from an external source, through an 5 inflation port 240 at the operator end of the catheter 210, to an inflatable balloon 214 located at or near the distal end of the catheter body 210. The inflation lumen 216 is defined by an annular space between the luminal surface of the catheter body 210 and the abluminal surface of the guidewire shall 222. A capture sheath 217 is provided at the distal end 215 of the catheter body 210 and is positioned adjacent and distal the balloon 214. The capture sheath 10 217 defines an annular space about the guidewire lumen 212 and the capture sheath 217 into which the sterit valve 10, 40 or 50 is positioned and retained during delivery. An annular plug member 220 is within the inflation lumen 216 distal the balloon 214 and terminates the inflation lumen 216 in a fluid tight manner. Annular plug member 220 has a central annular opening 221 through which the guidewire shaft 222 passes. The annular plug member 220 is 15 coupled to the guidewire shaft 222 and is moveable axially along the central longitudinal axis of the catheter 200 by moving the guidewire shaft 222. The annular plug member 220 also serves to abut ihc stent valve 10, 40 and 50 when the stent valve 10, 40 and 50 is positioned within the capture sheath 217. The guidewire shaft 222 passes through the capture sheath 217 and terminates with an atraumatic tip 218 which facilitates endolurninal delivery without 20 injuring the native tissue encountered during delivery. With this configuration, the stent valve is exposed by proximally withdrawing the catheter body 210, while the guidewire shaft 222 is maintained in a fixed position, such that the annular plug member 220 retains the position of the stent valve as it is uncovered by capture sheath 217 as the capture sheath 217 is being proximally withdrawn with the catheter body 210. 25 In many cases the anatomic valve will be significantly stenosed, and the valve flaps of the anatomic valve will be significantly non-compliant. The stenosed valves may be incapable of complete closure permitting blood regurgitation across the anatomic valve. *rhus. it may be desirable to configure the inflatable balloon 214 to assume an inflation profile which is modeled to maximally engage and dilatate the anatomic valves. For 30 example, a tricuspid valve, such as the aortic valve may stenose to an opening which has a gcerally triangular configuration. In order to maximally dilatate this triangular opening, it -28may be desirable to employ a balloon profile which assumes a triangular inflation profile. Alternatively, it may be advantageous to configure the balloon such that it does not fully occlude the anatomic lumen when inflated, but permits a quantum of blood flow to pass around the balloon in its inflated state. This may be accomplished by providing channels or 5 ridges on the abluminal surface of the balloon. Additionally, irregular inflation profiles of the balloon may facilitate continuous blood flow about the inflated balloon. Firthermore, ii may be desirable to configure the balloon to have an hour-glass inflation ponfile to prevent migration or slippage of the balloon in the anatomic valve during valvuloplasty. In accordance with the present invention, it is preferable that the capture sheath 217 10 be made of a material which is sufficiently strong so as prevent the stent valve 10, 40, 50 from impinging upon and seating into the capture sheath 217 due to the expansive pressure exerted by the stent valve 10, 40, 50 against the capture sheath. Alternatively, the capture sheath 217 may be lined with a lubricious material, such as polytetrafluoroethylene, which will prevent the capture sheath 217 from exerting drag or frictional forces against the stent 15 valve during deployment of the stent valve. In accordance with the present invention, it is also contemplated that the position of the balloon 214 and the capture sheath 217 may be reversed, such that the balloon 214 is distal the capture sheath 217. In this configuration, the anatomic valve may be radially enlarged by dilatating the balloon 214, then the catheter moved distally to position the 20 capture sheath 217 at the anatomic valve and deployed in the manner described above. This would also allow for post-deployment balloon expansion of the deployed stent valve without the need to traverse the prosthetic valve in a retrograde fashion. Alternatively, the catheter 200 of the present invention may be provided without a balloon 214 in those cases where valvuloplasty is not required. e.g., where a stenotic valve does not need to be opened such as 25 with a regurgitating valve, and the catheter 200 is terminated at its distal end with only a capture sheath 217, and deployment occurs as described above. Turning now to Figures 20A-201 there is illustrated the sequence of steps in delivery of the stent valve of the present invention, valvuloplasty of the aortic valve and deployment of the stent valve at the position of the aortic valve. The single catheter delivery system 501 30 having a distal balloon 502 and a capture sheath 503 covering the valve stent 10 (not shown in Figs 20A-B), is delivered percutaneously either through a femoral or subclavian artery -29approach, and traverses the aorta and is passed through the aortic valve 510 such that the balloon 503 on the distal end of catheter 501 is adjacent the aortic valve 510 and the capture sheath 503 is within rhe len ventricle 504. A valvuloplasty step 520 is performed by inflating balloon 503 to dilate the aortic valve and deform the aortic valve flaps against (he 5 aora wall adjacent the aortic valve. Afler the valvuloplasty step 520, delivery of the valve stent 505 is initiated by stabilizing the guidewire shaft (not shown) while the catheter body is withdrawn. antegrade relative to the blood flow until the proximal anchor flange section of the valve stent 505 is exposed by the withdrawal of the capture sheath 503. The distal anchor flange of the valve stent 505 is then positioned at the junction between the aortic valve and 10 the lefl ventricle at step 540, such that the distal anchor flange engages the ventricular surface of the aortic valve. The valve stent is fully deployed at step 550 by retrograde withdrawal of the catheter body 501 which continues to uncover the intermediate annular section of the valve stent and release the aortic valve stent 505. at the aortic valve site 510. In step 560, the valve stent 505 is completely deployed from the catheter 501 and the capture sheath 503. 15 The distal anchor section of the valve stent 505 expands and contacts the luminal wall of the aorta, immediately distal the aortic valve, thereby excluding the aortic valve flaps from the lumen of the prosthetic aortic valve stent 505. In step 570, the atraumatic tip and guidewire are retracted by retrograde movement of the guidewire shaft of the catheter, and the catheter 501 is withdrawn from the patient. Figures 20H and 201 depict the implanted valve stent 505 20 during diastole and systole, respectively. During ventricular diastole 580, the left ventricle expands to draw blood flow 506 from the left atrium into the left ventricle. A resultant negative pressure gradient is exerted across the valve stent 505, and the valve arms and valve flaps 506 of the valve stent 505 are biased to the closed position to prevent a regurgitation flow 507 from passing through the valve stent 505 and into the left ventricle 504. During 25 ventricular systole 590, the left ventricle contracts and exerts a positive pressure across the valve stent 505, which overcomes the bias of the valve arms and valve flaps. which open 508 against the luminal wall of the intermediate annular section of the valve stent and permit the ejection fraction 509 to be ejected from the left ventricle and into the aorta, The method for delivery of the CC valve stent 40 or the VV valve stent 50 is identical 30 to that of the CV stcnt 10 depicted in Figures 20A-201, except that the anatomical location wherc delivery and deployment of the valve stent occurs is, of course, different. -30- Thus, while the present invention, including the different embodiments of the valve stent, the delivery and deployment method and the single catheter valvuloplasty and delivery system, have been described with reference to their preferred embodiments, those of ordinary skill in the art will understand and appreciate that the present invention is limited in scope 5 only by the claims appended hereto.

Claims

1. A method of delivering a valve stent including the steps of: positioning a catheter body comprising a capture sheath retaining 5 the valve stent and a guidewire shaft comprising a plug member adjacent an anatomic valve; withdrawing the catheter body while the guidewire shaft is maintained in a fixed position such that the plug member retains a position of the valve stent and the valve stent is deployed over the anatomic valve. 10

2. The method according to claim 1 further including the step of positioning a distal anchor flange of the valve stent at a junction of the anatomic valve. 15

3. The method according to claim 1 or claim 2 further including the step of inflating a balloon comprised within the catheter body to dilatate the anatomic valve.

4. The method according to claim 3 wherein the step of inflating 20 includes communicating an inflation fluid through an inflation lumen in the catheter.

5. The method according to any preceding claim further including the step of retracting the guidewire shaft. 212322 1.DOC 33

6. The method according any preceding claim wherein the withdrawal of the catheter body is proximal.

7. The method according to any preceding claim wherein the 5 withdrawal of the catheter body is distal.

8. The method according to any preceding claim wherein at least a portion of the valve stent is comprised of a biocompatible material selected from the group consisting of metals and pseudometals. 10

9. The method according to any preceding clam wherein the valve stent includes at least one valve flap member comprised of a biocompatible material selected from the group consisting of metals and pseudometals. 15

10. A method of delivering a valve stent substantially as herein described with reference to any one of the embodiments of the invention as illustrated in the accompanying drawings and/or examples. 20

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