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    • 专利摘要:
    HIGH RESISTANCE DURABLE POLYMERIC COMPOSITE SUITABLE FOR IMPLANT AND ARTICLES PRODUCED FROM ITA biocompatible film made of high-strength composite material is described and suitable for use in various implant configurations. In one aspect, the composite material maintains flexibility in high flexural applications, making it particularly applicable to high flexibility implants: such as cardiac stimulation or cardiac valve leaflet. The composite material includes a porous expanded fluorinated polymer membrane and an elastomer, where the elastomer is present in virtually all pores of the expanded porous fluorinated polymer, and the composite material comprising less than about 80% by weight of fluorinated polymer.
    公开号:BR112013025114A2
    申请号:R112013025114-0
    申请日:2012-03-30
    公开日:2021-01-05
    发明作者:William C. Bruchman；Paul D. Gassler；Cody L. Hartman；Peter J. Walsh；Charles F. White
    申请人:W. L. Gore & Associates, Inc.；
    IPC主号:
    专利说明:

    "HIGH DURABLE POLYMERIC COMPOSITE SUITABLE RESISTANCE FOR IMPLANT AND ARTICLES PRODUCED FROM IT ”
    BACKGROUND OF THE INVENTION Field of the Invention The invention relates to materials used in medical implants. More particularly, the invention relates to a biocompatible material suitable for use in high flexion cycle applications, including artificial heart valves.
    STATE OF THE TECHNIQUE Artificial heart valves should preferably last at least ten years in vivo. To last, artificial heart valves must have sufficient durability for at least four hundred million cycles or more. Valves and, more specifically, heart valve leaflets, must withstand structural degradation, including the formation of holes, tears, and the like, as well as adverse biological consequences, including calcification and thrombosis. Fluoropolymers, such as expanded and unexpanded forms of polytetrafluoroethylene (PTFE), modified PTFE, and PTFE copolymers, offer a number of desirable properties, including excellent inertia and biocompatibility, and are therefore ideal materials. PTFE and expanded PTFE (ePTFE) have been used to create heart valve leaflets. However, it has been shown that PTFE hardens with repeated flexing, which can lead to unacceptable flow performance. Failure due to the formation of holes and tears in the material was also observed. A variety of polymeric materials have previously been employed as prosthetic heart valve leaflets. The failure of these leaflets due to stiffening and hole formation occurred within two years of implantation. Efforts to improve the durability of the leaflet by thickening the leaflets resulted in unacceptable hemodynamic performance of the valves, that is, the pressure drop across the open valve was too high. Therefore, it remains desirable to provide a biocompatible artificial heart valve that will last more than 10 years, in vivo, exhibiting sufficient durability for at least about four hundred million flexion cycles or more.
    SUMMARY OF THE INVENTION In accordance with one aspect of the invention, an implantable article is provided for regulating the direction of blood flow in a human patient. In one embodiment, the article includes an implantable leaflet comprising a composite material with at least one layer of fluorinated polymer having a plurality of pores and an elastomer present in substantially all pores at least one layer of fluorinated polymer in which the composite material 5 comprises less than about 80% by weight of fluorinated polymer. In another embodiment, the implantable article includes a support structure, a leaflet supported on the support structure and movable between the open and closed positions to regulate blood flow through the implantable article, and a damping element located at least between a portion of the support structure and at least a part of the leaflet, wherein the damping element is formed from a composite material with at least one layer of fluorinated polymer having a plurality of pores and an elastomer present in virtually all pores . In another embodiment, the implantable article generally includes an annular support structure having a first end and an opposite second end. The first end of the support structure has a longitudinally extending post. A leaflet of leaflet material extends along the outer periphery of the support structure and forms first and second leaflets that extend along opposite sides of the post. A damping element is attached to the post and provides cushioning between the post and the leaflets to minimize the stress and wear of the leaflets as the leaflets cycle between the open and closed positions.
    BRIEF DESCRIPTION OF THE FIGURES The accompanying Figures are included to provide a better understanding of the invention and are incorporated and form a part of this specification, illustrate embodiments of the invention and, together with the description serve to explain the principles of the invention. Figures 1A, 1B, 1C and 1D are front, side and top views, seen in perspective, respectively, of a tool for forming a cardiac valve leaflet; Figure 2A is a perspective view of a damping block stretched across a booklet tool; Figure 2B is a perspective view of a release layer being extended along a damping block covered by the booklet tool in Figure 2A; Figures 3A, 3B and 3C are from the top, side and front elevation views illustrating a step in the formation of a valve membrane, in which the leaflet tool covered by the damping block and the release layer (shown in Figures 2A and 28, respectively) is positioned on a composite material for cutting and then together; Figure 4 is a top elevation view of a set of tri-pamphlets before cutting excess leaflet material; Figure 5A is a perspective view of the tri-leaflet and a basic tool set.
    Figure 5B is a perspective view of the tri-leaflet set and a base tool aligned and assembled to form a base tool set; Figure 6A is a plan view of a stent frame or support structure; Figure 6B is a plan view of the support structure covered by a polymer coating; Figures 7A, 7B and 7C are scanned electron micrograph images of expanded fluorine polymer membranes used to form the valve leaflets.
    Figure 8 is a perspective view of a valve assembly; Figures 9A and 9B are top elevation views of the heart valve assembly of Figure 8 shown illustratively in the closed and open positions, respectively; Figure 10 is a graph of the results measured from a heart pulse duplicator system flow used to measure the performance of the valve assemblies; Figures 11 A and 11 B are a graph and a graph of results data measured from a high rate fatigue tester used to measure the performance of valve assemblies; Figures 12A and 12B are graphs of measured results of the pulsation doubling system flow made when testing valve assemblies according to the invention, zero cycles and after about 207 million cycles, respectively. Figures 13A and 13B are graphs of measured results of the flow of the heartbeat duplicator system carried out when testing valve assemblies in about 79 million cycles and after about 198 million cycles,
    respectively; Figure 14 is a perspective view of a mandrel for manufacturing a heart valve assembly; Figure 15 is a perspective view of a valve structure for a heart valve; Figure 16 is a perspective view of the valve structure of Figure 15 fitted together with the mandrel Figure 14; Figure 17 is a perspective view of a molded valve; Figure 18 is a perspective view of a molded valve, showing a fastener for reinforcing the connection between the adjacent valve leaflets and a post of a valve frame; Figure 19 is a perspective view of a valve structure; Figure 20 is a perspective view of the valve structure of Figure 19, with posts that are rolled up with damping; Figure 21 is a perspective view of a mandrel - formed by stereolithography; Figure 22 is a perspective view of the cushioned coiled valve structure of Figure 20 mounted on the mandrel of Figure 21; and Figure 23 is a perspective view of a valve that has valve leaflets attached and supported on the cushioned valve structure of Figure 20. DETAILED DESCRIPTION OF METHODS
    ILLUSTRATED Definitions of some terms used here are provided below in the appendix. The present invention addresses a long-felt need for a material that meets the durability and biocompatibility requirements of high-flexion implant applications, such as heart valve leaflets. It has been observed that cardiac valve leaflets formed from porous materials or fluorine polymers, more particularly, from ePTFE not containing elastomer, suffer from rigidity in high flexion and animal implant testing cycles. In one embodiment, described in more detail below, the flexural durability of the porous fluorinated polymer heart valve leaflets has been significantly increased by the addition of a high percentage of an elastomer of lower pore resistance. Optionally, additional layers of the elastomer can be added between the layers of the composites. Surprisingly, in embodiments where porous membranes of fluorinated polymer are embedded with the elastomer, the presence of the elastomer increases the overall thickness of the leaflet, resulting in the increase in the thickness of the fluorinated polymer elements, due to the addition of the elastomer does not affect or decrease flexural durability. In addition, after reaching a minimum weight percent of elastomer, it was found that fluorinated polymer elements in general perform better with increasing elastomer percentages, resulting in a significant increase in the life cycle of more than 40 million in vitro cycles, as well as showing no signs of calcification under certain controlled laboratory conditions. A material according to an embodiment includes a composite material comprising an expanded fluorinated polymer membrane and an elastomeric material. It should be readily appreciated that various types of fluorine polymer membranes and various types of elastomeric materials can be combined, while within the spirit of the present invention. It should also be readily appreciated that the elastomeric material can include various elastomers, various types of non-elastic components, such as inorganic fillers, therapeutic agents, radiopaque markers, and at the same time, as within the spirit of the present invention. In one embodiment, the composite material comprises a material made of fluorinated polymer made from a porous ePTFE membrane, for example, as described generically in U.S. Patent No.
    7,306,729. The expandable fluorinated polymer, used to form the described expanded fluorinated polymer material, may comprise PTFE homopolymer. In alternative embodiments, blends of PTFE, modified expanded PTFE and / or expanded PTFE copolymers can be used. Non-limiting examples of suitable fluorine polymer materials are described, for example, U.S. Patent No. 5,708,044, White, U.S. Patent No. 6,541,589, Baillie, U.S. Patent No. 7,531,611, to Sabol et al., US Patent Application No. 11/906, 877, Ford, and the US patent application No. 12 / 410,050, to Xu et al. The expanded fluorinated polymer of the present invention can comprise any suitable microstructure to achieve the desired leaflet performance.
    In one embodiment, the expanded fluorinated polymer may comprise a microstructure of fibrillate interconnected nodes, as described in U.S. Patent No. 3,953,566 to Gore.
    In one embodiment, the microstructure of an expanded fluorinated polymer membrane comprises nodes interconnected by 5 fibrils, as shown in the scanning electron microscopy image in Figure 7A.
    The fibrils extend from the nodes in a plurality of directions, and the membrane has a generally homogeneous structure.
    Membranes with this microstructure can typically exhibit a tensile strength ratio of the matrix in two orthogonal directions, less than 2, and possibly less than 1.5. In another embodiment, the expanded fluorinated polymer may have a microstructure substantially only of fibrils, such as, for example, illustrated in Figures 7B and 7C, as is generally taught in U.S. Patent No. 7,306,729, to Bacino.
    Figure 7C is a larger enlargement of the expanded fluorinated polymer membrane shown in Figure 7B, and shows more clearly the homogeneous microstructure having substantially only fibrils.
    The expanded fluorinated polymer membrane that has substantially only fibrils, as shown in Figures 7B and 7C, may have a large surface area, such as greater than 20m2 / g, or greater than 25m2 / g, and, in some embodiments, may provide a highly balanced strength material having a matrix tensile strength product in two orthogonal directions of at least 1.5 x 105 MPA2, and / or a ratio of matrix tensile strength in two orthogonal directions, less than 2, and possibly less than 1.5. The expanded fluorinated polymer of the present invention can be adapted to have any suitable thickness and mass to obtain the desired performance leaflet.
    In some cases, it may be desirable to use a very thin membrane of expanded fluorinated polymer, with a thickness of less than 1.0 µm.
    In other embodiments, it may be desirable to use an expanded fluorinated polymer membrane having a thickness greater than 0.1 µm and less than 20 µm.
    Expanded fluorinated polymer membranes may have a specific gravity of less than about 1g / m2 to greater than about 50g / m2. The membranes according to an embodiment of the invention can have a tensile strength of the matrix ranging from about 50 MPa to about 400 MPa or higher, based on a density of about 2.2 g / cm 3 for the PTFE.
    Additional materials can be incorporated within the pores of the material or within the membranes or between the layers of membranes to improve the desired properties of the leaflet.
    Compounds according to one embodiment can include fluorinated polymer membranes having thicknesses ranging from about 500 µm to less than 0.3 µm.
    The expanded fluorinated polymer membrane combined with 5 elastomer provides the elements of the present invention, with the performance attributes required for use in high flexural cycle applications such as heart valve leaflets, in at least several significant ways.
    For example, the addition of the elastomer improves the fatigue performance of the leaflet, eliminating or reducing the stiffness observed with ePTFE materials.
    In addition, the likelihood of the material undergoing permanent deformation, such as wrinkling or crease, which could result in compromised performance is reduced.
    In one embodiment, the elastomer occupies substantially the entire volume of pores or spaces within the porous structure of the expanded fluorinated polymer membrane.
    In another embodiment, the elastomer is present in substantially all pores of at least one layer of fluorinated polymer.
    Having elastomer filling the pore volume or being present substantially in all pores reduces the space in which foreign materials can be undesirably incorporated into the compound.
    An example of such a foreign material is calcium.
    If calcium becomes incorporated into the composite material, such as used in a cardiac valve leaflet, for example, mechanical damage may occur during the cycle, thus leading to the formation of holes in the leaflet and degradation in hemodynamics.
    In one embodiment, the elastomer that is combined with that of ePTFE is a thermoplastic copolymer of tetrafluoroethylene (TFE) and perfluoromethyl vinyl ether (PMVE), as described in U.S. Patent No. 7,462,675. As discussed above, the elastomer is combined with the expanded fluorinated polymer membrane in such a way that the elastomer occupies substantially all of the void space or pores within the expanded fluorinated polymer membrane.
    This filling of the pores of the expanded fluorinated polymer membrane with elastomer can be accomplished by a variety of methods.
    In one embodiment, a method of filling the pores of the expanded fluorinated polymer membrane includes the steps of dissolving the elastomer in a suitable solvent to create a solution with a viscosity and surface tension that is suitable for the partial or total flow inside of the pores of the expanded fluorinated polymer membrane and allow the solvent to evaporate, leaving the filler material behind.
    In another embodiment, a method of filling the pores of the expanded fluorinated polymer membrane includes the steps of supplying filler material by means of a dispersion to completely or partially fill the pores of the expanded fluorinated polymer membrane.
    In another embodiment, a method of filling the pores of the expanded fluorinated polymer membrane includes the steps of bringing the porous expanded fluorinated polymer membrane 5 into contact with an elastomer leaflet, under conditions of heat and / or pressure that permit the elastomer flow into the pores of the expanded fluorinated polymer membrane.
    In another embodiment, a method of filling the expanded fluorinated polymer membrane pores includes the polymerization steps of the elastomer inside the pores of the expanded fluorinated polymer membrane first by filling the pores with an elastomer prepolymer and then at least partially cure the elastomer.
    After reaching a minimum percentage by weight of elastomer, leaflets constructed from fluorinated polymer or ePTFE materials generally perform better with increasing elastomer percentage, resulting in a significant increase in life cycle.
    In one embodiment, the elastomer combined with the thermoplastic ePTFE is a vinyl ether copolymer tetrafluoroethylene and perfluoromethyl, as described in U.S. Patent No. 7,462,675. For example, in another embodiment shown in Example 1, a leaflet was formed from a composition of 53% by weight of ePTFE elastomer and was subjected to the cycle test.
    Some hardening has been observed in about 200 million cycle tests, but with only a modest effect on hydrodynamics.
    When the weight percentage of the elastomer was increased to about 83% by weight, as in the embodiment of Example 2, no hardening or negative changes in hydrodynamics were observed in about 200 million cycles.
    In contrast, with non-composite leaflets, that is, all ePTFE without elastomer, as in Comparative Example B, severe hardening was apparent for 40 million test cycles.
    As demonstrated by these examples, the durability of the porous fluorinated polymer elements can be significantly increased by adding a relatively high percentage of elastomer of resistance relatively less than that of the pores of the fluorinated polymer elements.
    The high strength of the fluorinated polymer membrane material also allows specific configurations to be very thin.
    Other biocompatible polymers that may be suitable for use in the present invention may include, but are not limited to, groups of urethanes, silicones (organopolysiloxanes), silicone - urethane copolymers, styrene / isobutylene copolymers, polyisobutylene, polyethylene-co-poly ( vinyl acetate), polyester copolymers, nylon copolymers, fluorinated hydrocarbon polymers and copolymers or mixtures of each of the above. The following non-limiting examples are provided to further illustrate embodiments of the present invention.
    Example 1 Heart valve leaflets according to one embodiment were formed from a composite material with an expanded fluorinated polymer membrane and an elastomeric material and joined to an expandable, metallic balloon, as described by the following process: 1) A thick, cushioning or layer tool was formed by folding a layer over itself over ePTFE to create a total of four layers.
    The ePTFE layer was about 5 cm (2 ") wide, about 0.5 mm (0.02") thick and had a high degree of compression, forming a cushioning block.
    Referring to Figures 1 and 2, damping block 200 was then stretched (Figure 2) for a booklet tool, generically indicated by 100. Booklet tool 100 has a booklet portion 102, a body portion 104 and a lower end 106. the leaflet portion 102 of the leaflet tool 100 has a generally arcuate, convex end surface 103. The damping block 200 has been stretched and smoothed over the end surface 103 of the leaflet portion 102 of the leaflet tool 100 by forcing the booklet tool 100 in the direction represented by the arrow (Figure 2A). A peripheral edge 202 of the cushion block 200 was stretched over the lower end 106 of the booklet tool 100 and twisted to hold the cushion block 200 in place (Figure 2B). 2) Referring to Figure 2B, a release layer 204 was then stretched over the leaflet portion 102 of tool 100, which in the previous step was covered with damping block 200. In one embodiment, the release layer 204 was made from a substantially non-porous ePTFE, having a layer of fluorinated ethylene-propylene (FEP), arranged along an external surface or on its side.
    The release layer 204 has been stretched over the leaflet tool 100 in such a way that the faced FEP layer for the damping block 200 and the substantially non-porous ePTFE faced outside or away from the damping block 200. The release layer is about 25 µm thick and of sufficient length and width to allow the release layer 204 to be pulled over the lower end 106 of the booklet tool 100. As with the buffer block 200 in the previous step, a peripheral edge 206 of release layer 204 was pulled to the lower end 106 of the booklet tool 100 and then twisted to the lower end 106 of the booklet tool 100 to hold or hold the release layer 204 in place.
    The FEP release layer of layer 204 was then melted and thereby fixedly attached to the damping block 200, as needed, using a hot soldering iron. 3) The processes from steps 1) and 2) were repeated to prepare three separate leaflet tools, each having a damping block covered by a release layer. 4) A leaflet material according to one embodiment was formed from a composite material that comprises an ePTFE membrane embedded with a fluorinated elastomer.
    A portion of the composite material approximately 10 cm wide was wound in a circular mandrel to form a tube.
    The composite material was composed of three layers: two outer layers of ePTFE and an inner layer of a fluorinated elastomer placed between them.
    The ePTFE membrane was manufactured in accordance with the general teachings described in U.S. Patent No. 7,306,729. The fluorinated elastomer was formulated in accordance with the general teachings described in U.S. Patent No. 7,462,675. Additional fluoro elastomers may be suitable and are described in US Publication No. 2004 / 0024448. The ePTFE membrane had the following properties: thickness = about 15 µm; MTS in the direction of force majeure = about 400 MPa; MTS in the direction of orthogonal force = about 250 MPa; density = about 0.34 g / cm3; IBP = about 660 kPa.
    The copolymer consists essentially of about 65 and 70% by weight of perfluoromethyl vinyl and in addition about 35 and 30% by weight of tetrafluoroethylene.
    The weight of fluorinated elastoemetry in relation to ePTFE was around 53%. The multi-layered compound had the following properties: Thickness of about 40 µm; density of about 1.2 g / cm3; breaking strength / width in the direction of greater force = about 0.953 kg / cm, tensile strength in the direction of greater force = about 23.5 MPa (3,400 psi); breaking strength / width in the orthogonal direction = about 0.87 kg / cm, tensile strength in the orthogonal direction = about 21.4 MPa (3100 psi), IPA bubble point greater than about 12.3 MPa, Gurley number greater than about 1,800 seconds and mass / area = about 14 g / m2. The following test methods were used to characterize the ePTFE layers and the multi-layer composite.
    The thickness was measured with a Mutitoyo absolute pressure Gage, 12.7 mm (0.50 ") meters in diameter, model ID-C112E, Serial # 10299, made in Japan.
    Density was determined by a weight / volume calculation using a Mettler PM400 analytical balance New Jersey, USA.
    Breaking strength and tensile strength was measured using a # 5500R Norwood, MA lnstron model, 50 kg load cell, Length gauge = 25.4 cm, crosshead speed = 25mm / minute (strain rate = 100% per minute) with flat face jaws.
    The Bubble Point IPA was measured by an IPA bubble point tester, Data Systems model LG-Apok industrial pressure regulator, Salt Lake City, UT, USA, with a ramp rate of 1.38 kPa / s (0.2 psi / s), 3.14 cm2 test area.
    Gurley N was determined as the time in seconds for 100 cm3 of air to flow through a 6.45 cm2 sample of 124 mm of water pressure using a Gurley apparatus, Model # 4110, Troy, NY, USA.
    Unless otherwise indicated, these test methods were used to generate the data in the following examples.
    The layers of composite material, each having two outer layers of ePTFE and an inner layer of a fluorinated elastomer placed between them, was wrapped in a mandrel that has a diameter of about 28mm (1.1 ") in such a way that the direction of greater force of the membrane was oriented in the axial direction of the mandrel.
    In one embodiment, four layers of the composite material have been wrapped in a non-helical shape, generally circular over the mandrel.
    The composite material had a slight degree of viscosity that allowed the material to adhere to itself.
    While still in the mandrel, the composite material was cut longitudinally, generally along the longitudinal axis of the mandrel to form a leaflet of about 10 cm (4 ") by about 90mm (3.5"). 5) The resulting leaflet of leaflet material (or composite material from Step 4) was then cut and rolled over the tool, the leaflet tool 100 having a damping block 200 covered by a release layer 204. More specifically, as shown in Figures 3A-3C, the leaflet material 300 was placed on a flat cutting surface.
    The leaflet tool
    100 with the damping block 200 and 204 of the release layer were then aligned on the material of the booklet 300 approximately as shown.
    Four slits 302, 304, 306, 308 were then formed in the leaflet material 300 with a blade.
    A pair of slots 302, 304 extends from one side of the tool 5 leaflet 100 and ends at one edge 300a of the leaflet material 300, and the other pair of slits 306, 308 extends from an opposite side of the booklet tool 100 and ends an opposite end 300b of the booklet material 300. Slots 302, 304, 306, 308 have been moved away from booklet portion 102 of booklet tool 100. Slots 302, 304, 306, 308 do not protrude under the booklet tool 100. It should be checked that the widths of the individual slits do not show the scale.
    Slits 302, 304, 306, 308 in the leaflet material 300 resulted in the formation of a folding portion 310, a pair of straps 312, 314 and excess leaflet material 315. Folding portions 310 were folded in the direction indicated by the arrows 316 in Figure 3 and on the leaflet tool 100, which was covered by the damping block 200 and the release layer 204 in the previous steps. 6) The excess of booklet material 315 was stretched and smoothed over the booklet portion 102, in particular the end surface 103 of the booklet tool 100. Steps 4) and 5) were repeated to form three separate booklet assemblies.
    The sets of three leaflets 402, 404, 406 were then attached to form a set of mounting tri-leaflets 400, as shown in Figure 4. The three separate sets of leaflets 402, 404, 406 are shown, each having an excess of booklet material 315 which extends generically radially beyond the periphery of tri-booklet assembly 400. 7) The base tool was then provided with cavities to enclose the final surfaces of the booklet tools of the tri-booklet assembly and trim excess booklet area to form three booklets.
    Referring to Figure 5A, the base tool is generally indicated by 500 and extends longitudinally between a lower end 501 and an opposite end 503. Three concave cavities 502, 504, 506 are formed at the end 501 of the base tool 500. Each concave cavity 502, 504, 506 is formed to match a nested seat or end surface 103 of one of the three brochure sets 402, 404, 406. The three radially extending elements 508, 510, 512 extend out from the end of the base tool 500. Each of the elements 508, 510, 512 is arranged between an adjacent pair of concave cavities 502, 504, 506. The base tool 500 was then prepared with a block release layer and compression layer (not shown), similar to the way the booklet tool was prepared in Steps 1 and 2. As described for each booklet tool in Steps 1 and 2, compression damping and the release layer were likewise stretched and attached to the base tool 500 to form a base tool set. 8) Referring to Figure 5B, the base set of the tool (illustrated for convenience, as the base tool 500 without showing the damping block and release layer) and the tri-leaf set, usually indicated at 400, were , then generally axially aligned together so that the end surface (not shown) of each leaflet tool 100 has been fitted to that of the concave cavities (not shown) at the end 501 of the base tool, usually indicated at 500, to the set tool combination. 9) An expandable metallic balloon was then manufactured.
    A 316 stainless steel tube having a wall thickness of about 0.5mm (0.020 ") in diameter of about 2.5 centimeters (1.0) was laser cut.
    A pattern was cut into the tube to form an annular cutting stent or support structure, which is generally indicated at 600 and shown illustratively in a flat surface view in Figure 6a.
    The support structure 600 includes a plurality of small closed cells 602, a plurality of large closed cells 604, and a plurality of closed leaflet cells 606. Note that one of the plurality of closed cell leaflet 606 appears as a open cell in Figure 6A due to the flat surface view.
    Cells 602, 604, 606 are generally arranged along the lines that form the annular shape of the support structure 600. 10) Polymeric materials were then glued to the laser cut stent board.
    First, a sacrificial compression layer of the ePTFE membrane was wound without overlapping over a mandrel (not shown), having a diameter of about 2.5 cm (1.0 "). The sacrificial compression layer of the ePTFE membrane had a thickness of about 0.5mm (0.02 ") and a width of about 10 cm (4"), and was compatible and compressible to provide a soft sacrificial compression layer. 11) Four layers of a substantially non-porous ePTFE film was then wound into the mandrel on top of the compression membrane layer.
    The substantially non-porous ePTFE film was about 25 µm (0.001 ") thick, about 10 cm (4") wide and had a layer of FEP on one side.
    The substantially non-porous ePTFE film was wrapped with FEP facing away from the mandrel.
    The substantially non-porous ePTFE film had the properties of the release layer as described previously in step 2). 12) A thin film of type 1 (ASTM D3368) FEP was constructed using melt extrusion and elongation. 10 additional layers of this type 1 thin film (ASTM D3368) FEP was added to the mandrel, which was previously wound on the compression layer membrane in step 10 and Four layers of a substantially non-porous ePTFE film from step 11. The thin film of type 1 (ASTM D3368) FEP had a thickness of about 40 µm (0.0016) and a width of about 7.7 cm (3 "). 13) The coiled mandrel was then heat treated by a convection oven. air at about 320 ° C for about 5 minutes and allowed to cool 14) The support structure (indicated at 600 in Figure 6A) was then placed over the heat treatment and the rolled mandrel.
    Two layers of thin film type 1 (ASTM D3368) FEP (supplied in step 12) were then rolled over the support structure, which was previously placed over the rolled mandrel. 15) The rolled mandrel and the support structure supported on it were then heat treated in an air convection oven at about 320 ° C for about 10 minutes and allowed to cool, forming a coated polymeric support structure. 16) The coated polymeric support structure was then cut with a scalpel to form a cut stent frame, which is usually indicated by 700 and shown illustratively in a flat surface view in Figure 6B.
    More specifically, in one form, the polymeric coating was trimmed about 2 mm (0.08 ") beyond the ends of the support structure (600, Figure 6A) to form a variety of edge profiles 708. In another way, the coating polymeric was allowed to cover whole cells to form a web in each cell.
    In both cases, the support structure 600 was fully encapsulated within a polymeric coating 702, to form a cut stent frame 700. The cut stent frame 700 includes a plurality of leaflet openings 704 corresponding to the number and generally in the form of a plurality of closed cells of leaflet 606 (Figure 6A). In addition, a groove groove groove 706 is formed in the polymeric coating 702 of each of the small closed cells, as shown in Figure 6B.
    Specifically, each groove 706 is linear and generally parallel to a central longitudinal axis (not shown) of the ring-shaped support structure 600. 17) The cut stent frame was then placed on the combined tool assembled in step 8. The portions leaflet (102) of the leaflet tools were aligned with the leaflet openings (704 in Figure 6B) in the O 5 stent cut frame.
    The three areas of excess material (leaflet 315 in Figure 4) were pulled through the leaflet openings of the cut stent frame.
    Each of the three pairs of straps (312, 314 in Figure 3A), were pulled through one of them (slot 706 in Figure 6B) and wrapped around the cut stent frame.
    Each pair of straps was packed in opposite directions from the other.
    The six straps were then heat nailed to the stent frame cut using a hot soldering iron. 18) The combined tool set (Step 8) cut stent frame having the wrapped and heat-taped straps was then mounted on a rotating mandrel mechanism.
    The rotating mandrel mechanism was then adjusted to apply a longitudinal light compression load.
    The areas of excess leaflet material (315 in Figure 4) were then nailed to the base tool (500 in Figure 5), using a hot soldering iron. 19) The combined tools from step 18 were then wrapped with an additional two layers of type 1 (ASTM 03.368) FEP film (from step 12). Three additional layers of the composite (Step 4) were then wrapped and glued to the trimmed stent structure. 20) In preparation for a final heat treatment, release and sacrificial layers of a compression tape and compression fibers were applied both circumferentially and longitudinally to the assembly of step 19. The compression tape / fiber contacts and compresses the assembly both circumferentially and longitudinally during the subsequent heat treatment.
    The sacrificial layer of compression tape was circumferentially wrapped in a helical shape in the assembly from step 19. This compression tape had the properties of the ePTFE sacrifice compression layer previously described in step 10. An ePTFE compression fiber was then wrapped in compression tape.
    About 100 loops of compression fiber were circumferentially applied in a narrowly spaced helical pattern.
    The compression ePTFE fiber was about 1mm (0.04 ") in diameter and was structured to shrink longitudinally, when sufficiently heated.
    The clamped assembly was then removed from the rotating mandrel mechanism.
    Three layers of sacrificial compression tape were then wrapped longitudinally around the assembly.
    Approximately 20 wraps of the compression fiber were then wound longitudinally along the longitudinal compression tape. 21) The assembly of step 20 was then treated by the heat of an air convection oven device at about 280º C for about 90 minutes and then water at room temperature satiated.
    This heat treatment step facilitates the flow of the fluorinated thermoplastic into the pores of the ePTFE membrane used to create the leaflet material described in step 4. 22) The sacrificial compression tapes / fibers were then removed.
    The polymeric materials were trimmed to allow the booklet and base tools to be separated.
    The polymeric stent layers were then cut to allow removal of the stent frame with attached leaflets.
    The leaflets were then trimmed, resulting in a valve assembly, as shown in Figure 8, and generally indicated at 800. The resulting valve assembly 800, according to one embodiment, includes 802 leaflets formed from a composite material with at least one layer of fluorinated polymer having a plurality of pores and an elastomer present in substantially all pores of the layer of at least one fluorinated polymer.
    Each leaflet 802 is movable between a closed position, shown illustratively in Figure 9A, where blood is prevented from flowing through the valve assembly, and an open position, shown illustratively in Figure 9B, where blood is allowed to flow through the valve assembly. valve assembly.
    Thus, the leaflets 802 of the valve assembly 800 of the cycle between the open and closed positions to regulate the general direction of blood flow in a human patient.
    The performance of the valve leaflets in each valve assembly was characterized in a real-time pulse duplicator that measured typical anatomical pressures and flows through the valve, generating an initial threshold or "zero fatigue" of data for the particular valve assembly.
    The valve assembly was then transferred to a high-frequency fatigue tester, and underwent about 207 million cycles.
    After each block of about 100 million cycles, the valve was then returned to the pulse duplicator in real time and the performance parameters were measured again.
    Flow performance was characterized by the following process: 1) The valve assembly was filled into a silicone annular ring (support structure) to allow the valve assembly to be subsequently evaluated in a pulse duplicator in real time.
    The filling process was carried out according to the recommendations of the pulse duplicator manufacturer (ViVitro Laboratories lnc., Victoria BC, Canada). 2) The bottled valve assembly was then placed in a cardiac flow pulse duplicator system in real time.
    The flow pulse duplicator system included the following components supplied by VSI Vivitro Sistemas lnc, Victoria BC, Canada: a Supe pump, Power Amplifier Servo of the part SPA 3891, a Super Head pump.
    Part number SPH 5891B, 38,320 cm2 of cylinder, one valve / clamp station; a waveform generator, Tripack Part number TP 2001; a Sensor interface, Part Number VB 2004, a Sensor Amplifier component, Part number AM 9991, and a square wave Electro magnetic flowmeter, Carolina Medical Electronics lnc, East Bend, NC, USA.
    In general, the doubling system uses a fixed displacement pulse flow, the piston pump, to produce a desired fluid flow through the valve under test. 3) The flow of the heart pulse duplicator system was adjusted to produce the desired flow, pressure and simulated pulse.
    The valve under test was then cycled for about 5 to 20 minutes. 4) Pressure and flow data were measured and collected during the test period, including ventricular pressures, aortic pressures, flow rates and piston pump position.
    Shown illustratively in Figure 10 is a graph of typical flow data results from the cardiac pulse duplicator system. 5) The parameters used to characterize the valve and to compare it with the post-fatigue values are the pressure drop across the open valve during the forward positive pressure flow portion, the effective orifice area, and the fraction of regurgitation.
    After characterization, the valve assembly was then removed from the flow pulse doubling system and placed on a high frequency fatigue tester.
    The Durability Position Six Heart Valve Tester, Part Number M6 was supplied by Dynatek, Galena, MO, USA, and was powered by a Dynatek Dalta DC 7000 Controller.
    This high fatigue rate tester displaces fluid through a valve assembly with a typical cycle rate of around 780 cycles per minute.
    During the test, the valve assembly can be examined visually using a tuned strobe light.
    The pressure drop through the closed valve can also be monitored as shown in Figures 11A and 11B.
    Shown in Figures 11A and 11B is a typical data set verifying that the higher fatigue tester was producing consistent pressure waveforms. 5 The valve assembly was continuously cycled and periodically monitored to release visual changes and pressure.
    After about 200 million cycles, the valve assembly was removed from the high frequency tester and returned to the pulse duplicator in real time.
    The pressure and flow data were collected and compared with the original data collected.
    Figure 12A shows a screen capture of the typical measured data output from the heart pulse duplicating system flow in real time.
    Ventricular pressures, aortic pressures and flow are shown.
    The initial fatigue or zero data for a particular valve is shown illustratively in Figure 12A.
    The same measurements were taken and data were collected for the same valve after 207 million cycles.
    The 207 million cycle data for the special valve is shown illustratively in Figure 12B.
    Both sets of measurements were taken at 5 liters per minute flow and at a rate of 70 cycles per minute.
    Comparing Figures 12A and 12B, it should be readily understood that the waveforms are substantially similar, indicating that there were no significant changes in the valve's leaflet performance after about 207 million cycles.
    The pressure drop, the effective orifice area (EOA), and the regurgitation fraction measured at zero and 207 million cycles are summarized in Table 1 below.
    Number of Pressure Drop EOA (cm2) Fraction of cycles (million) (mm Hg) regurgitation (%) 0 5.7 2.78 12.7 207 7.7 2.38 9.6 TABLE 1 In general, we observed It is understood that the valve leaflets constructed in accordance with the embodiments described here do not exhibit physical or mechanical degradation, such as tears, holes, permanent deformation and the like, after 207 million cycles.
    As a result, there was also no observable change or degradation in the closed and open configurations of the valve leaflets, even after 207 million cycles.
    Example 2 A heart valve having polymeric leaflets attached to a rigid metallic structure was constructed according to the following process: A mandrel 900 was machined from PTFE with a shape shown in Figure 14. Mandrel 900 has a first end 902 and a second opposite end 904, and extends longitudinally between them. The mandrel 5 has an outer surface which has 91O three (two shown), in general, arched convex lobes 912, each in general for forming leaflets (not shown) of a finished valve assembly (not shown). The outer surface 910 also includes a 920 seating area frame for positioning a valve frame (930 in Figure 15) in relation to the convex lobes 912 prior to the formation of the valve leaflets for the weft. As shown in Figure 15, a valve structure 930 was laser cut from a length of 316 stainless steel tube with an outer diameter of about 25.4 mm and a mural thickness of about 0.5 mm in the shape shown in Figure 15. In the embodiment shown, the weft valve 930 extends axially between a lower end 932 and an opposite upper end generally defined by a plurality of which extend axially, generally in the form of spire messages 934 corresponding to the number of leaflets in the desired finished valve assembly (not shown). In the specific embodiment shown, three stations 934 are formed on the valve thread
    930. Two layers of a film about 4 mm thick FEP (not shown) was wrapped around the 930 thread valve and baked in an oven for about 30 minutes at about 270 º C and allowed to cool. The resulting covered weir valve (for clarity, shown uncovered and indicated at 930) was then slid upward onto the mandrel 900, so that the complementarity characteristics between the 930 valve and the mandrel 900 wedge are fitted together, as shown in Figure 16 A leaflet material was then prepared with a layer of ePTFE membrane soaked with fluorine. More specifically, the ePTFE membrane layer was manufactured in accordance with the general teachings described in U.S. Patent No. 7,306,729. The ePTFE membrane was tested in accordance with the methods described in the Appendix. The ePTFE membrane had a mass per area of about 0.57 g / m2, a porosity of about 90.4%, a thickness of about 2.5 µm, a dot bubble of about 458 kPa, a resistance to the matrix traction of about 339 MPa, in the longitudinal direction and of about 257 MPa, in the transverse direction. This membrane was soaked with fluorinated scab as described in Example 1. The fluorinated was dissolved in Novec HFE7500, 3M, St. Paul, MN, USA, in a 2.5% concentration. The solution was coated using a Mayer bar over the ePTFE membrane (while being supported by a polypropylene release film) and dried in a defined convection oven 5 at about 145 º C for about 30 seconds. After two coating steps, the resulting ePTFE / fluorinated composite material had a mass per area of about 3.6 g / m2. The composite material (not shown) was then wound around the frame-mounted mandrel 900 and valve 930. In embodiment, a total of 20 layers of the ePTFE / fluorinated compound was used. Any excess composite material that extended beyond the ends of the mandrel 900 was twisted and lightly pressed against the ends 902, 904 of the mandrel 900. The composite material of the rolled mandrel was then mounted in a pressure vessel so that a discharge port 906 (Figure 14) at the base or second end 904 of mandrel 900 has been probed into the atmosphere. The vent 906 extends from the second end 904 axially through the mandrel 900 and communicates with a vent opening that generally extends perpendicularly 908 extending through the outer surface 910 of the mandrel 900. Vent holes 906, 908, in addition to other ventilation ports, which can be provided in the mandrel as needed (not shown), allow the air trapped between the composite material and the mandrel to escape during the molding process. About 690 kPa (100 psi) of nitrogen pressure was applied to the pressure vessel, forcing the ePTFE / fluorinated compound against the mandrel 900 and the valve stem 930. Heat was applied to the pressure vessel until the temperature inside the reactor reached about 300 º C, about 3 hours later. The heater was turned off and the pressure vessel was allowed to cool to room temperature overnight. This process thermally bonded the composite ePTFE / fluorinated layers to each other and to the FEP coating on the valve thread
    930. The pressure was released and the mandrel was removed from the pressure vessel. The ePTFE / fluorinated compound was cut circumferentially at two points: first, at the lower end 932 of the stem valve 930, and second, near the upper end of the stem valve 930 along a circle generally intersecting near the midpoint of each post 934. The valve assembly 940, resulting consisting of valve 930 and trimmed weft the composite material was separated and slid out of the mandrel The valve molded assembly
    940, as shown in Figure 17, includes the weft valve 930 and a plurality of blades 950 formed from trimmed composite material.
    In one embodiment, the valve assembly 940 includes three cusps.
    In another embodiment, each leaflet 950 in the 940 valve assembly was approximately 5 40 mm thick.
    To help control the degree of openness of the valve, adjacent leaflets on each post were glued together.
    As shown in Figure 18, adjacent leaflets 950a, 950b were wrapped around post 934 and connected together to form a seam 954. Seam 954 had a depth 956 extending to at least about 2 mm from of post 934. To support the link between adjacent leaflets 950A, 950B, attachment element 952 was rigidly fixed to internal surfaces of adjacent leaflets 950A, 950b bridge, thus seam 954 between adjacent leaflets 950A, 950B.
    As shown in Figure 18, the fixture 952 is generally rectangular.
    And it should be appreciated, however, that other shapes for the fastener can be used.
    The fixture 952 was formed from the type of composite material scab used to form the 950 leaflets. The fixture 952 was rigidly attached to the interior surfaces of the adjacent cusps 950a, 950b, using the fluorinated solution described above.
    These steps were repeated for the other adjacent cusp pairs in the valve assembly.
    The performance and durability of the valve leaflets in this example were analyzed in the scab form as described in Example 1. The valve assembly was initially characterized in the real-time scab duplicator as described in Example 1, which was measured typical anatomical pressures and flows through the valve, to generate an initial "zero fatigue" or data set for that particular valve set.
    The valve was then subjected to accelerated tests that in Example 1. After about 79 million cycles, the valve was removed from the high rate fatigue test device and the hydrodynamic performance again characterized as in Example 1. The valve was finally removed in about 198 million cycles.
    The pressure drop, (EOA), and fractional regurgitation measured at about 79 million cycles and about 198 cycles are summarized in Table 2 below.
    Figures 13A and 13B show similar results for a similar valve.
    Figure 13A is a graph of the measured output data from the pulsation doubling system flow made after about 79 million cycles.
    Measurements were taken for similar valve scab after about 198 million cycles, a graph of which is shown illustratively in Figure 13B.
    Both sets of measurements were taken at about 4 liters per minute and flow rates of around 70 cycles per minute.
    By comparing Figures 13A and 13B, it should again be appreciated that the waveforms are significantly similar, indicating that there were no significant changes in the leaflet performance of valve 5 after about 198 million cycles.
    The pressure drop, the effective orifice area (EOA), and the regurgitation fraction measured at about 79, and about 198 million cycles are summarized in Table 2 below.
    These data indicate no substantial change in the performance of the valve leaflet after approximately 198 million cycles.
    Number of Pressure Drop EOA (cm2) Fraction of cycles (million) (mm Hg) regurgitation (%) 0 6.8 2.56 7.8 79 5.4 2.58 10.25 198 4.4 2.60 10.01 TABLE 2 Example 3 A heart valve having polymeric leatlets that joined a rigid metallic wire was constructed according to the following process: The support structure of the 960 valve or wire was laser cut to a length for the 316 stainless steel with an outside diameter of about 25.4 mm or a wall thickness of about 0.5 mm in the form shown in Figure 19. In embodiment shown, wire 960 extends axially between a lower end 962 and an opposite upper end generally defined by a plurality that extends axially, usually in the form of 964 spire messages corresponding to the number of cusps in the valve assembly that is intended to terminate (not shown). The parabolically shaped upper end 968 extends between adjacent messages 964. In the specific embodiment shown, three posts 964 and three top edges 968 form the upper end of wire 960. The corners of the wire that would be in contact with the leaflet material were rounded using a rotary sander and hand polished.
    The frame was rinsed with water and then clean plasma using a PT2000P plasma treatment system, Tri-Star Technologies, El Segundo, CA, USA.
    In one embodiment, a damping element is provided between at least a portion of the weft and at least a part of the leaflet to minimize the stress related to direct contact between the weft and the leaflet.
    The composite fiber ot ePTFE and silicone was created by the first by soaking an ePTFE membrane with MED -6215 silicone (NuSi, Carpinteria, CA, USA), cut to a width of about 25 mm, and rolling in a substantially round udder.
    The ePTFE used in this fiber has been tested in accordance with the methods described in the Appendix.
    The ePTFE membrane had a dot bubble of about 217 kPa, 5 a thickness ot about 10 pm, the mass per unit area of about 5.2 g / m2, a porosity of about 78%, a resistance to tensile strength of the matrix in a direction of about 96 MPa, and a tensile strength matrix of about 55 MPa in the orthogonal direction.
    The fiber composite 966 was wrapped around each of the posts of the 964, 960 wire, as shown in Figure 20. A mandrel 970 was formed using stereolithography in a shape shown in Figure 21. Mandrel 970 has a first end 972 and a second opposite end 974, and extends longitudinally therebetween.
    Mandrel 970 has an outer surface 980 having three (two shown) generally arched convex lobes 982, each in general for forming leaflets (not shown) of a finished valve assembly (not shown). The outer surface 980 also includes a weft seating area 984 for positioning the weft (960 in Figure 19) in relation to the convex lobes 982 prior to the formation of the valve leaflets on the weft valve.
    The 970 mandrel was then spray coated with a PTFE release agent.
    Four layers of the ePTFE membrane previously described in this example were wrapped around the mandrel.
    MED -6215 was swept in the ePTFE and allowed to get wet and to substantially fill the pores of the ePTFE.
    Excess MED -6215 has been erased and branch 960 with the fiber composite of 966 wrapped messages 964 has been positioned on mandrel 970 along the joint area of branch 984, as shown in Figure 22. Of MED-4720 silicone, NuSil, Carpinteria , CA, USA, has been placed along the upper edges 968 of wire 960 and 964 along the wire 960 messages to create strain relief in the leatlet (not shown). Eight additional layers of ePTFE were wrapped around the wire 960 and mandrel 970. Additional MED -6215 was swept into the ePTFE and allowed to get wet and to substantially fill the pores of the ePTFE.
    Another 8 layers of ePTFE were wrapped around the wire 960 and mandrel 970. These layers were blotter-shaped to absorb any excess silicone during the molding process and were removed after the silicone had cured.
    Forms of silicone rubber (not shown) molded with a surface exactly matching the reverse shape of the mandrel surface were previously manufactured for each of the three leaflet forming characteristics.
    These spray forms were coated with PTFE to release the mold and then coupled with the mandrel matching feature.
    About 5 of 50 turns of an ePTFE fiber (not shown), were wrapped around the silicone molds to apply generically radial pressure, to the valve against the mandrel.
    This set was then placed in an oven at about 100 º C for about 1 hour to cure the silicone.
    After cooling, the silicone fiber forms and were removed, the eight layers of the ePTFE blotter were peeled off and discarded, and the resulting valve (not shown) was slid out of the mandrel.
    The pins were cut using pliers and the excess length of the leaflet material and the excess length of the material at the base of the frame was carefully trimmed with scissors to form a completed valve assembly, which is shown and generally indicated in 990 in Figure 23. Thus, in one embodiment, valve assembly 990 was formed having the frame or support structure 960, a plurality of blades 992 supported on the support structure 960 and movable between the open and closed positions to regulate flow of blood through valve assembly 990; and a compound 966 involved fiber post 964 located between at least a portion of the support structure 960 and at least a portion of each leaflet 992 to minimize stress on the leaflets due to coupling and / or proximity of the cusps to the support structure.
    In another embodiment, the damping element is formed from a composite material with at least one layer of fluorinated polymer having a plurality of pores and an elastomer present in virtually all pores, as described above.
    And it should be appreciated that others that as support structures specifically shown in can be used in the Figures.
    In addition, the damping elements can be used anywhere along the support structure, as necessary to minimize stress on the leaflets due to coupling and / or proximity of the cusps to the support structure.
    For example, a damping element (s) can be attached to the support structure along the upper edge in parabolic shape.
    And it should also be appreciated that the damping elements can be formed like leaflets and wrapped around desired locations along the support structure, or be formed from fibers of various shapes and sizes in cross section.
    The LT should also be appreciated that the damping elements can be formed like tubes and slid along the ends of the support structure, or be cut longitudinally and positioned around the desired location along the support structure.
    The complete valve leaflets were measured and determined to have an average thickness in the center of each leaflet of about 120 µm.
    The valve assembly was then characterized by the flow performance and subjected to accelerated testing as in Example 1. After each block of about 50 million cycles, the valve assembly was removed from the high rate fatigue testing device and the hydrodynamic performance again characterized as in Example 1. The valve assembly was finally removed in about 150 million cycles and demonstrated acceptable performance and no hole formation.
    Comparative Example Six valves were constructed in the manner of Example 1 with the exception that the elastomer was not incorporated.
    The ePTFE material was the same as described in Example 1, but it was not soaked with the fluorinated copolymer and was instead coated with a discontinuous layer of FEP copolymers that served as a thermoplastic adhesive.
    The valves were constructed as in Example 1, with each leaflet comprising three layers of membrane resulting in an average final leaflet thickness of about 20 µm.
    After hydrodynamic characterization, the valves were mounted on the Dynatek accelerated test device described in Example 1. For about 40 million cycles, the end delamination and hole formation in the leaflets was observed and the test was stopped.
    Comparative Example B Two valves were constructed in the manner of Example 1, but without incorporating the elastomer portion of the invention.
    The material used was that of the thin ePTFE membrane that has properties similar to the following: a mass per unit area of about 2.43 g / m2, a porosity of about 88%, an IBP of approximately 4.8 kPa, a thickness of about 13.8 µm, a tensile strength of the matrix in a direction of about 662 MPa and a tensile strength of the matrix of about 1.2 MPa, in the orthogonal direction.
    The ePTFE membrane has been tested in accordance with the methods described in the Annex.
    Ten layers of the membrane were placed in alternating directions in a pile and then
    placed on the tools, such as. The three pieces of tools were then inserted into the stent frame and the leaflets attached to the valve assembly with FEP as in Example 1. Each of the valves was subjected to high rate fatigue tests using the cardiac pulse duplicator system. real time as described above. After about 30 million cycles on one valve and about 40 million cycles on another valve, visual degradation, including stiffness and deformation, was observed and measurable with decreased performance noted. And in addition to the visual and measurable degradation in performance, Table 3 below summarizes the pressure drop, the effective orifice area (EOA), and the regurgitation fraction measured after about 40 million cycles. Number of cycles EOA pressure drop (cm2) Fraction of (million) (mm Hg) regurgitation (%) 0 3.9 3.11 8.1 40x106 6.5 2.85 14.1 TABLE 3 AND will be evident for the skilled in the art that various modifications and variations can be made to the present invention without departing from the spirit or scope of the invention. Thus, it is intended that the present invention covers the modifications and variations of this invention as long as they are within the scope of the appended claims and their equivalents.
    ANNEX As used in this application, matrix tensile strength refers to the resistance to removal of a sample of porous fluorinated polymer under specified conditions. The porosity of the sample is counted by multiplying the tensile strength by the ratio of the density of the polymer to the density of the specimen. As used herein, the term "membrane" refers to a porous fluorinated polymeric article, "compound" refers to embedded porous fluorinated polymers, and a "leaflet" is a component of an implant article for regulating the direction of the blood flow. Leaflets of the present invention are one or more layers of a compound. The term "absorb" used herein refers to any process used to at least partially fill the pores with secondary material. For fluorinated porous polymer leaflets with pores substantially filled with the elastomer, the elastomer can be dissolved or degraded and washed with a suitable solvent in order to measure the desired properties.
    As the term "elastomer" is used here, it defines a polymer, mixture of polymers, or mixtures of one or more polymers with one or more 5 non-polymeric components that have the ability to be stretched at least 1.3 times the its original length and retracts quickly to approximately its original length when released.
    The term "elastomeric" is intended to describe a polymer property which exhibits elastomer-like stretch and recovery properties, although not necessarily to the same extent and / or recovery.
    Since the term "thermoplastic" is used here, it defines a polymer that softens when exposed to heat and returns to its original state when cooled to room temperature.
    Such a polymer can be made to soften, drain or take on new forms, without significant degradation or change in the original state of the polymer, through the application of heat or heat and pressure.
    In contrast to a thermoplastic polymer, a "thermoset" polymer is defined herein as a polymer that solidifies or "remains" irreversibly when cured.
    The determination of whether a polymer is a "thermoplastic" polymer within the meaning of the present invention can be made by slowly raising the temperature of a stressed specimen and observing deformation.
    If the polymer can be made to soften, flow, or take on a new shape, without any significant degradation or change in the polymer's original chemical condition, then the polymer is considered to be a thermoplastic.
    If only small amounts of material are obtained, it may be necessary to use a hot stage under a microscope for this determination.
    A measure of the quality of a valve is the effective area of the orifice (EOA), which can be calculated as follows: EOA (cm2) = Qms I (51.6 * (∆) 1/2) where Qms is the square root systolic mean / diastolic flow (cm3 / s) and OP is systolic / drop in diastolic pressure (mmHg). As used in this patent application, the surface area per unit of mass, expressed in units of m2 / g, was measured using the method on a Coulter SA3100Gas Adsorption Analyzer Beckman Coulter LNC by Brunauer- Emmett-Teller (BET). Fullerton CA, USA.
    To perform the measurement, the sample was cut from the center of the expanded fluorinated polymer membrane and placed in a small sample tube. the sample mass was about 0.1 to 0.2 g. The tube was placed in the Coulter SA -Prep Superficial Outgasser Area (Model SA-Prep, P / N 5102014) from Beckman Coulter, Fullerton CA, USA and purged at about 110 C for about two hours with helium. The test tube was then removed from the SA -Prep Outgasser and weighed. The test tube was then placed in the SA3100 gas adsorption analyzer and the BET surface area analysis was performed in accordance with the instrument instructions using helium to calculate the free space and nitrogen as the adsorbed gas. Bubble Point and average pore size flow were measured according to general teachings of ASTM F31 6-03 using a capillary flow porometer, Model CFP 1500AEXL of Porous Materials, lnc. Ithaca, NY, USA. The membrane sample was placed in the sample chamber and wetted with SilWick silicone fluid (available from Porous Materials lnc.) Having a surface tension of about 20.1 dynes / cm. The bottom clip of the sample chamber was about 2.54 cm in diameter. Using the Capwin software version
    7.73.012 the following parameters were arrows indicated in the table below. Parameter Set Point Maxflow (cm3 / m) 200000 Bublflow (cm3 / m) 100 F / PT (formerly bubltime) 50 Minbpress (PSI) 0 zero time (sec) 1 V2incr (CTS) 10 Preginc (CTS) 1 pulse delay ( sec) 2 Maxpre (PSI) 500 pulse width (sec) 0.2 Mineqtime (sec) 30 Presslew (CTS) 10 Flowslew (CTS) 50 Eqiter 3 Aveiter 20 Maxpdif (PSI) 0.1 Maxfdif (PSI) 50 Sartp ( PSI) 1 Sartf (cm3 / m) 50 Membrane thickness was measured by placing the membrane between the two Kafer plates FZ1000 / 30 gauge pressure thickness Kafer Messuhrenfabrik GmbH, Villingen-Schwenningen, Germany. The average of the three measures was reported.
    The presence of elastomer within the pores can be determined by several methods, such as the surface and / or visual cross section, or other analyzes.
    These analyzes can be performed before and after removing the elastomer from the leaflet.
    Membrane samples were cut to form rectangular sections about 2.54 cm by about 15.24 cm to measure weight (using the Mettler-Toledo analytical balance model AG204) and thickness (using a Kafer Fz1000 / 30 pressure gauge) . Using these data, the density was calculated with the following formula: p = m / w * l * t, where: p = density (g / cm3: m = mass (g), w = width (cm), l = length (cm), t = thickness (cm) .The average of the three measurements was reported.
    Tensile breaking load was measured using an INSTRON 122 tensile testing machine equipped with flattened grips and a 0.445 kN load cell.
    The duration was about 5.08 cm and the crosshead speed was about 50.8 centimeters / min.
    The dimensions of the samples were about 2.54 centimeters by 15.24 centimeters.
    For longitudinal measurements, the longest dimension of the sample was oriented in the direction of maximum force.
    For orthogonal MTS measurements, the largest sample size was oriented perpendicular to the direction of the maximum force.
    Each sample was weighed with a Mettler Toledo model scale AG204, then the thickness measured using the Kafer FZ1000 / 30 pressure gauge. The samples were then tested individually on the tensile tester.
    Three different sections of each sample were measured.
    The average of the three maximum loads (ie the peak force) measurements were reported.
    The longitudinal and transverse matrix (STM) tensile strengths were calculated using the following equation: STM = (maximum load of / cross-sectional area) * (bulk density PTFE) / (the density of the porous membrane), where the bulk density of PTFE was made to be about 2.2 g / cm3. Flexural stiffness was measured following the general procedures set out in ASTM 0790. Unless large test samples are available, the test sample must be reduced.
    The test conditions were as follows.
    The leaflet specimens were measured in a three-point flexion tester using sharp messages placed horizontally about 5.08 mm from each other. A steel bar about 1.34 mm in diameter, weighing about 80 mg was used to cause deformation in the y direction (downward), and the samples were not contained in the x direction.
    The steel bar was placed slowly over the central point of the membrane sample.
    After waiting about 5 minutes, deflection y was measured.
    Deflection of supported elastic beams as above can be represented by: d = * F * L3 / 48 EI, where F (in Newtons) is the load applied at the center of the beam length, L (in meters), then L = 1 / 2 distance between the suspension posts, and El is the flexural stiffness (Nm). From this relationship the EI value can be calculated.
    For a rectangular cross section: 1 = t3 * w / 12, where l = moment of inertia cross section, t = sample thickness (m), w = sample width (meters). With this relationship, the mean elastic modulus in the flexural strain measurement range can be calculated.
    权利要求:
    Claims (42)
    [1]
    1. Prosthetic valve characterized by comprising: a plurality of movable leaflets between the open and closed positions, each leaflet comprising a plurality of layers of composite material, the composite material having at least one layer of fluorinated polymer having a plurality of pores and an elastomer present substantially in all pores of at least one layer of fluorinated polymer, wherein the plurality of layers of the composite material are coupled with a layer of the elastomer between each plurality of layers of the composite material.
    [2]
    Prosthetic valve according to claim 1, characterized in that the composite material comprises less than about 70% by weight of fluorinated polymer.
    [3]
    Prosthetic valve according to claim 1 or claim 2, characterized in that the composite material comprises less than about 60% by weight of fluorinated polymer.
    [4]
    Prosthetic valve according to any one of claims 1 to 3, characterized in that the composite material comprises less than about 50% by weight of fluorinated polymer.
    [5]
    Prosthetic valve according to any one of claims 1 to 4, characterized in that the elastomer is a fluorinated elastomer.
    [6]
    Prosthetic valve according to claim 5, characterized in that the elastomer is a TFE / PMVE copolymer.
    [7]
    Prosthetic valve according to claim 6, characterized in that the copolymer essentially comprises between about 40 and 80 weight percent perfluoromethyl vinyl ether and in addition 60 and 20 weight percent tetrafluoroethylene.
    [8]
    Prosthetic valve according to any one of claims 1 to 7, characterized in that the fluorinated polymer is PTFE.
    [9]
    Prosthetic valve according to claim 8, characterized in that PTFE is ePTFE.
    [10]
    Prosthetic valve according to any one of claims 1 to 9, characterized in that at least one layer of fluorinated polymer has a tensile strength of the matrix in at least one direction greater than about 96 MPa.
    [11]
    Prosthetic valve according to any one of claims 1 to 10, characterized in that the elastomer is a TFE /
    PMVE.
    [12]
    Prosthetic valve according to claim 11, characterized in that the copolymer essentially comprises between about 40 and 80 weight percent perfluoromethyl vinyl ether and in addition 60 and 20 weight percent tetrafluoroethylene.
    [13]
    Prosthetic valve according to any one of claims 1 to 12, characterized in that the leaflet is less than about 350 µm thick.
    [14]
    Prosthetic valve according to any one of claims 1 to 13, characterized in that the leaflet is less than about 300 µm thick.
    [15]
    Prosthetic valve according to any one of claims 1 to 14, characterized in that the leaflet is less than about 200 µm thick.
    [16]
    16. Prosthetic valve according to any one of claims 1 to 15, characterized in that the leaflet is less than about 100 µm thick.
    [17]
    Prosthetic valve according to any one of claims 1 to 16, characterized in that the leaflet is less than about 50 µm thick.
    [18]
    Prosthetic valve according to any one of claims 1 to 17, characterized in that the leaflet has a thickness of less than about 25 µm.
    [19]
    19. Prosthetic valve according to any of claims 1 to 18, characterized in that an EOA is maintained next to the prosthetic valve for regulating the direction of blood flow within about 10% after approximately 40 million cycles.
    [20]
    20. Prosthetic valve according to any one of claims 1 to 19, characterized in that a regurgitation fraction is maintained on the other side of the prosthetic valve for the regulation of the blood flow direction below about 15% after approximately 40 million cycles.
    [21]
    21. Prosthetic valve according to any one of claims 1 to 20, characterized in that the leaflet is free of delamination at the end or orifice formation after approximately 40 million cycles.
    [22]
    22. Prosthetic valve according to any one of claims 1 to 21, characterized in that the composite material comprises less than about 50% by weight of the fluorinated polymer.
    [23]
    23. Method of forming the prosthetic valve composite material of any one of claims 1 to 22, characterized in that it comprises: (a) dissolving an elastomer in an appropriate solvent to create a solution to substantially fill the pores of at least one layer of fluorinated polymer; (b) substantially filling the pores of at least one layer of fluorinated polymer; and (c) allowing the solvent to evaporate so that the elastomer remains substantially in all pores of the at least one layer of fluorinated polymer.
    [24]
    24. The method of claim 23, characterized in that in step (b) it comprises supplying the elastomer by means of a dispersion to substantially fill all pores of at least one layer of fluorinated polymer.
    [25]
    25. The method of claim 23, characterized by step (b) in that it comprises placing at least one layer of fluorinated polymer in contact with an elastomer leaflet under heat or pressure conditions that allow the elastomer to substantially fill all pores of at least one layer of fluorinated polymer.
    [26]
    26. The method of any one of claims 23 to 25, the method further characterized in that it further comprises the step of elastomer polymerization within the pores of at least one layer of fluorinated polymer.
    [27]
    27. Prosthetic valve for regulating the direction of blood flow in a human patient, the prosthetic valve characterized by comprising: a support structure; a leaflet supported on the support and mobile structure between the open and closed positions to regulate the blood flow through the prosthetic valve; and a damping element located between at least a portion of the support structure and at least a portion of the leaflet, wherein the damping element is formed from a plurality of layers of composite material, the composite material having at least one layer of fluorinated polymer, the fluorinated polymer having a plurality of pores and an elastomer present in substantially all pores, wherein a plurality of layers of the composite material is coupled with a layer of the elastomer between each plurality of layers of the composite material.
    [28]
    28. Prosthetic valve according to claim 27, characterized in that the damping element includes expanded fluorinated polymer.
    [29]
    29. Prosthetic valve according to claim 27 or claim 28, characterized in that the damping element is formed as a fiber.
    [30]
    30. Prosthetic valve according to claim 27 or claim 28, characterized in that the damping element is formed as a leaflet.
    [31]
    31. Prosthetic valve according to claim 27 or claim 28, characterized in that the damping element is formed as a tube.
    [32]
    32. Prosthetic valve according to claim 29, characterized in that the damping element is generally helically wrapped over at least a portion of the support structure to provide damping between at least a portion of the support structure and at least a portion of the leaflet.
    [33]
    33. Prosthetic valve according to any one of claims 27 to 32, characterized in that the support structure includes a longitudinally extending pole on which a part of the leaflet is rolled up to secure the leaflet to the support structure.
    [34]
    34. Prosthetic valve according to any one of claims 27 to 33, characterized in that at least one layer of fluorinated polymer of the damping element is formed from porous ePTFE.
    [35]
    35. Prosthetic valve according to claim 32, characterized in that the fiber is formed from an ePTFE leaflet having a plurality of pores and an elastomer present in practically all pores.
    [36]
    36. Prosthetic valve for regulating the direction of blood flow in a human patient, the prosthetic valve characterized by comprising: a ring-shaped support structure, the support structure having a first end and an opposite second end, the first end having a pole that extends longitudinally; a sheet of leaflet material that extends along an outer periphery of the support structure and forms a first and a second leaflet that each extends along the opposite sides of the pole; and a cushioning element coupled to the post to provide cushioning between the post and the first and second leaflet, each leaflet comprising a plurality of layers of the composite material, the composite material having a plurality of layers having at least one layer of fluorinated polymer having a plurality of pores and an elastomer present substantially in all pores of at least one layer of fluorinated polymer, wherein the plurality of layers of composite material is coupled to the layer of the elastomer between each of the pluralities of layers of the composite material .
    [37]
    37. Prosthetic valve according to claim 36, characterized in that the damping element is a fiber formed from an ePTFE sheet that has a plurality of pores and an elastomer present in substantially all pores.
    [38]
    38. Prosthetic valve for regulating the direction of blood flow in a human patient, the prosthetic valve characterized by comprising: a plurality of movable leaflets between the open and closed positions, each layer comprising a plurality of layers of composite material, the composite material with at least one layer of fluorinated polymer having a plurality of pores and an elastomer that substantially fills the pores of the at least one layer of fluorinated polymer, wherein the plurality of layers of the composite material are coupled with an elastomer layer between each plurality layers of composite material, and
    [39]
    39. Implantable heart valve for regulating the direction of blood flow in a human patient, the heart valve characterized by comprising: a plurality of cyclable leaflets between a first configuration to allow blood flow through the implantable heart valve and a second configuration for substantially prevent blood flow through the implantable heart valve, each leaflet comprising a plurality of layers of composite material, composite material having at least one layer of fluorinated polymer having a plurality of pores and an elastomer present substantially in all pores of at least a fluorinated polymer layer, wherein the plurality of layers of composite material are coupled with the elastomer layer between each of the plurality of layers of composite material; and wherein the composite material is less than about 55% by weight of fluorinated polymer and less than 120 µm thick.
    [40]
    40. Implantable heart valve according to claim 39, characterized in that an EOA is maintained next to the implantable heart valve within about 10% after approximately 40 million cycles.
    [41]
    41. Implantable heart valve according to claim 39, characterized in that a fraction is kept next to the implantable heart valve below about 15% after about 40 million cycles.
    [42]
    42. Implantable heart valve according to claim 39, characterized in that each leaflet is free of delamination at the end or orifice formation after about 40 million cycles.
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    法律状态:
    2021-01-12| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|Free format text: REFERENTE AO ACESSO AO PATRIMONIO GENETICO NACIONAL |
    2021-01-12| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|
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    优先权:
    申请号 | 申请日 | 专利标题
    US13/078,774|US8961599B2|2011-04-01|2011-04-01|Durable high strength polymer composite suitable for implant and articles produced therefrom|
    US13/078.774|2011-04-01|
    PCT/US2012/031417|WO2012135603A2|2011-04-01|2012-03-30|Durable high strength polymer composite suitable for implant and articles produced therefrom|
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