Source: https://patents.google.com/patent/US20130238086A1/en
Timestamp: 2019-09-20 21:41:43
Document Index: 493273541

Matched Legal Cases: ['Application No. 61', 'Application No. 61', 'Application No. 61', 'Application No. 61', 'Application No. 61', 'Application No. 61', 'Application No. 61', 'Application No. 61', 'Application No. 61']

US20130238086A1 - Electrospun PTFE Encapsulated Stent & Method of Manufature - Google Patents
Electrospun PTFE Encapsulated Stent & Method of Manufature Download PDF
US20130238086A1
US20130238086A1 US13/743,668 US201313743668A US2013238086A1 US 20130238086 A1 US20130238086 A1 US 20130238086A1 US 201313743668 A US201313743668 A US 201313743668A US 2013238086 A1 US2013238086 A1 US 2013238086A1
US13/743,668
Sabrina D. Puckett
2009-01-16 Priority to US14530909P priority Critical
2009-08-07 Priority to US23225209P priority
2009-10-30 Priority to US25634909P priority
2010-01-19 Priority to US12/689,334 priority patent/US8178030B2/en
2010-08-09 Priority to US12/852,993 priority patent/US8262979B2/en
2010-08-09 Priority to US12/852,989 priority patent/US8257640B2/en
2010-10-14 Priority to US39312810P priority
2011-09-23 Priority to US201161538402P priority
2011-10-13 Priority to US13/272,412 priority patent/US8685424B2/en
2012-04-13 Priority to US13/446,300 priority patent/US20130023175A1/en
2012-08-02 Priority to US13/564,927 priority patent/US9034031B2/en
2012-08-02 Priority to US13/564,925 priority patent/US20130059497A1/en
2012-09-24 Priority to US13/625,548 priority patent/US20130079700A1/en
2013-01-17 Application filed by Zeus Industrial Products Inc filed Critical Zeus Industrial Products Inc
2013-01-17 Priority to US13/743,668 priority patent/US20130238086A1/en
2013-03-06 Assigned to ZEUS INDUSTRIAL PRODUCTS, INC. reassignment ZEUS INDUSTRIAL PRODUCTS, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: ANNEAUX, BRUCE L., BALLARD, ROBERT L., GARNER, DAVID P., MANASCO, JOSHUA L., PUCKETT, Sabrina D.
2013-09-12 Publication of US20130238086A1 publication Critical patent/US20130238086A1/en
A stent or other prosthesis may be formed by encapsulating a scaffold or frame with a polymer coating. The polymer coating may consist of layers of electrospun polytetrafluoroethylne (PTFE). Electrospun PTFE of certain porosities may permit endothelial cell growth within the prosthesis. The stent may be applicable to stents designed for the central venous system, peripheral vascular stents, abdominal aortic aneurism stents, bronchial stents, esophageal stents, biliary stents, or any other stent.
U.S. patent application Ser. No. 13/446,300, filed Apr. 13, 2012, which application is a continuation of U.S. patent application Ser. No. 12/689,334, filed Jan. 19, 2010, (now U.S. Pat. No. 8,178,030), which application claims the benefit of U.S. Provisional Patent Applications Nos. 61/145,309, filed Jan. 16, 2009, and 61/256,349, filed Oct. 30, 2009;
U.S. patent application Ser. No. 13/564,925, filed Aug. 2, 2012, which application is a continuation of U.S. patent application Ser. No. 12/852,989, filed Aug. 9, 2010, (now U.S. Pat. No. 8,257,640), which application claims the benefit of U.S. Provisional Patent Application No. 61/232,252, filed Aug. 7, 2009;
U.S. patent application Ser. No. 13/564,927, filed Aug. 2, 2012, which application is a continuation of U.S. patent application Ser. No. 12/852,993, filed Aug. 9, 2010, (now U.S. Pat. No. 8,262,979), which application claims the benefit of U.S. Provisional Patent Application No. 61/232,252, filed Aug. 7, 2009;
U.S. patent application Ser. No. 13/272,412, filed Oct. 13, 2011, which application claims the benefit of U.S. Provisional Patent Application No. 61/393,128, filed Oct. 14, 2010; and
U.S. patent application Ser. No. 13/625,548, filed Sep. 24, 2012, which application claims the benefit of U.S. Provisional Patent Application No. 61/538,402, filed Sep. 23, 2011.
The present disclosure relates generally to medical devices. More specifically, the present disclosure relates to stents or other prostheses.
FIG. 2A is a perspective view of a covered stent.
FIG. 2B is a cross sectional view of the stent of FIG. 2A along the plane 2B-2B.
FIG. 3 illustrates one embodiment of a stent deployed in a body lumen.
FIGS. 4A-4B are scanning electron micrograph (SEM) images of embodiment of an electrospun PTFE outer covering for a stent.
FIGS. 5A-5B are SEM images of an electrospun PTFE inner layer of the covering of the stent of FIG. 4A-4B.
FIGS. 6A-6B are SEM images of an electrospun PTFE outer covering of another embodiment of a stent.
FIGS. 7A-7B are SEM images of an electrospun PTFE inner layer of the covering of the stent of FIG. 6A-6B.
The entire disclosures of U.S. patent application Ser. No. 12/689,334, filed Jan. 19, 2010 (now U.S. Pat. No. 8,178,030), U.S. Provisional Patent Application No. 61/145,309, filed Jan. 16, 2009, U.S. Provisional Patent Application No. 61/256,349, filed Oct. 30, 2009, U.S. patent application Ser. No. 12/852,989, filed Aug. 9, 2010, (now U.S. Pat. No. 8,257,640), U.S. Provisional Patent Application No. 61/232,252, filed Aug. 7, 2009, U.S. patent application Ser. No. 12/852,993, filed Aug. 9, 2010, (now U.S. Pat. No. 8,262,979), U.S. patent application Ser. No. 13/272,412, filed Oct. 13, 2011, U.S. Provisional Patent Application No. 61/393,128, filed Oct. 14, 2010, U.S. patent application Ser. No. 13/625,548, filed Sep. 24, 2012, and U.S. Provisional Patent Application No. 61/538,402, filed Sep. 23, 2011, are incorporated herein by this reference as if set forth in their entireties.
Stents may be deployed in various body lumens for a variety of purposes. Stents may be deployed, for example, in the central venous system for a variety of therapeutic purposes including the treatment of occlusions within the lumens of that system. It will be appreciated that the current disclosure may be applicable to stents designed for the central venous (CV) system, peripheral vascular (PV abdominal aortic aneurism (AAA) stents, bronchial stents, esophageal stents, biliary stents, or any other stent. Further, the present disclosure may equally be applicable to other prosthesis such as grafts. Thus, the disclosure provided below in connection with specific examples of stents may apply analogously to other prostheses.
The phrases connected to, coupled to, and in communication refer to any form of interaction between two or more entities, including mechanical, electrical, magnetic, electromagnetic, fluid, and thermal interaction. Two components may be coupled to each other even though they are not in direct contact with each other. For example, two components may be coupled to each other through an intermediate component.
The directional terms proximal and distal are used herein to reference opposite locations on a stent. The proximal end of a stent is defined as the end of the stent closest to the practitioner when the stent is disposed within a deployment device which is being used by the practitioner. The distal end is the end opposite the proximal end, along the longitudinal direction of the stent, or the end furthest from the practitioner. It is understood that, as used in the art, these terms may have different meanings once the stent is deployed (i.e. the proximal end may refer to the end closest to the head or heart of the patient depending on application). For consistency, as used herein, the ends of the stent labeled proximal and distal prior to deployment remain the same regardless of whether the stent is deployed. The longitudinal direction of the stent is the direction along the axis of a generally tubular stent. In embodiments where a stent is composed of a metal structure coupled to a polymer layer, the metal structure is referred to as the scaffolding and the polymer layer as the coating. The term “coating” refers to a covering, typically fabric covering, that covers the scaffolding (or other frame) and, in many embodiments, encapsulates the frame inside and outside of the frame. “Coating” may refer to a single polymer, multiple layers of the same polymer, or layers comprising distinct polymers used in combination.
Electrospun polytetrafluoroethylene (PTFE) may be used as a stent coating where endothelial cell growth is desirable. Electrospinning refers to a process for forming mats, tubes, or other shapes by depositing small strings of PTFE on collection surfaces using electric potential. The electrospinning process controls the thickness, density, porosity, and other characteristics of the PTFE so formed. Electrospinning of PTFE is described in U.S. Pat. No. 8,178,030, which is incorporated herein in its entirety by this reference.
The present disclosure relates to a stent which has, in certain embodiments, metal scaffolding coated with at least one layer of electrospun PTFE. It will be appreciated that, though particular structures and coatings are described below, any feature of the scaffolding or coating described below may be combined with any other disclosed feature without departing from the scope of the current disclosure.
FIG. 1 shows a possible embodiment of a stent. FIGS. 2A and 2B illustrate an embodiment of a covered stent. FIG. 3 illustrates a stent deployed within a body lumen. Finally, FIGS. 4A-7B are scanning electron micrographs (SEMs) of possible coatings for stents. As indicated above, it will be understood that, regardless of whether the stent illustrated in any particular figure is illustrated with a particular coating, or any coating at all, any embodiment may be configured with any of the combinations of coatings shown or described herein.
FIG. 1 illustrates a front elevation view of an embodiment of a stent 100. The illustrated embodiment depicts one embodiment of a configuration for a metal wire 110 forming a scaffolding structure. This disclosure is not limited by any particular stent or frame or scaffolding structure.
Referring generally to FIG. 1, particular features of the illustrated stent are indicated. It will be appreciated that the numerals and designations used in any figure apply to analogous features in other illustrated embodiments, whether or not the feature is so identified in each figure. As generally shown in these Figures, the stent 100 may consist of a wire 110 shaped to form scaffolding. The wire 110 may be shaped in a wave-type configuration, the waves defining apexes 102 and arms 104 of the stent. The scaffolding may further be coupled to a covering layer (not pictured). Additionally, in some embodiments, any covering as disclosed herein may be applied to any type of scaffolding or stent frame, for example, laser cut stent frames, polymeric stent frames, wire scaffolding, and so forth.
The overall stent design may be configured to optimize desired radial force, crush profile, and strain profile. The stent design parameters may each be configured and tuned to create desired stent characteristics, as will be understood by those skilled in the art.
Referring now to FIGS. 2A and 2B, in some embodiments the stent 100 may be comprised of a wire 110 which forms the scaffolding and a cover 200 coupled to the scaffolding. In some embodiments this cover may be comprised of a single layer, while in other embodiments it may be comprised of 2, 3, or more layers of material. One or more layers may be comprised of a polymer.
The illustrated embodiment has two cover layers, an outer layer 210 and an inner layer 220.
In some embodiments the outer layer 210, the inner layer 220, or both may be comprised of electrospun PTFE. Electrospun PTFE consists of tubes, mats, or other shapes of PTFE formed from randomly deposited strings of PTFE. As previously indicated, electrospinning of PTFE is described in U.S. Pat. No. 8,178,030 and other disclosure that have been incorporated herein, above. As described in the reference, electrospinning may comprise depositing a polymer on a collection surface, in the presence of an electrostatic field. In some instances the polymer may be electrostatically charged and may be discharged through one or more orifices.
Further information relative to electrospinning PTFE or other polymer is included below. The properties of electrospun PTFE, including density and porosity, may be controlled or influenced during the creation of the electrospun PTFE, through controlling the electrospinning process.
In some embodiments, a fiberizing agent is added to an aqueous dispersion of PTFE particles, to aid in the formation of PTFE fibers during the process of electrospinning the material. In some exemplary embodiments, polyethylene oxide (PEO) may be added as the fiberizing agent to the PTFE dispersion prior to electrospinning the material. In some instances the PEO may more readily dissolve in the PTFE dispersion if the PEO is first mixed with water. In some examples this increased solubility may reduce the time needed to dissolve PEO in aPTFE dispersion from as long as multiple days to as little as 30 minutes. In some embodiments, the PTFE dispersion may be discharged through an orifice to electrospin the PTFE. In an alternative embodiment, the PTFE dispersion is electrospun (e.g., into a fabric sheet or coating) using an open bath electrospinning apparatus. For example, the apparatus can comprise a wire, cylinder, spike, sharp edge, or similar geometry spinning electrode that creates a perturbation. For the open bath (trough) unit, the ejection volume is dependent upon the viscosity of the dispersion, the conductivity of the dispersion, the surface tension of the dispersion, the distance from bath to target, and the voltage. For either of the embodiments, after the material is electrospun onto a collector, the material may then be sintered as further described below. In some instances the sintering process will tend to set or harden the structure of the PTFE. Furthermore, sintering may also eliminate the water and PEO, resulting in a mat of substantially pure PTFE.
In one exemplary process, Poly(ethylene oxide) (300,000 kDa-40 grams) was added to 1 L aqueous dispersion of PTFE (˜60 wt % PTFE) with a 230 nm average particle size (for example, Daikin DX-9025, available from Daikin Industries, Ltd.) and allowed to gel (˜5 days). The material was then rolled to combine (˜10 rpm) for at least 48 hours to produce a viscous, off-white dispersion. The combined mixture was then allowed to sit or mix on a non-agitating jar roller until the solution achieved homogeneity. In other examples, the water, PEO, and PTFE amounts may be controlled to optimize the viscosity, PEO/PTFE ratio, or other properties of the mixture. In some instances adding water to the PEO before mixing with the PTFE dispersion may aid in reducing the number of large solid chunks in the mixture, lower the preparation time for the mixtures, and reduce the time needed for the combined mixture to solubilize.
Nonwoven fabric composed of electrospun PTFE may have a microstructure composed of many fibers crossing each other at various and random points. The electrospinning process may control the thickness of this structure and, thereby the relative permeability of the fabric. As more and more strands of PTFE are electrospun onto a fabric, the fabric may both increase in thickness and decrease in permeability (due to successive layers of strands occluding the pores and openings of layers below). (This microstructure is shown in FIGS. 5A-7B, which are discussed in more detail below.)
The complex and random microstructure of electrospun PTFE presents a challenge to the direct measurement of the average pore size of the fabric. Average pore size can be indirectly determined by measuring the permeability of the fabric to fluids using known testing techniques and instruments. Once the permeability is determined, that measurement may be used to determine an effective pore size of the electrospun PTFE fabric. As used herein, the pore size of an electrospun PTFE fabric refers to the pore size of a fabric which corresponds to the permeability of the electrospun PTFE when measured using ASTM standard F316 for the permeability measurement. This standard is described in ASTM publication F316 Standard Test Methods for Pore Size Characteristics of Membrane Filters by Bubble Point and Mean Flow Pore Test, which is incorporated herein by reference.
In some applications it may be desirable to create a stent 100 with an outer layer 210 which is substantially impermeable. Such a layer may decrease the incidence of lumen tissue surrounding the stent growing into the stent. This may be desirable in applications where the stent is used to treat stenosis or other occlusions; an impermeable outer layer may prevent tissue from growing into the lumen of the stent and reblocking or restricting the body lumen. In some embodiments a substantially impermeable outer layer may be comprised of electrospun PTFE with an average pore size of about 0 microns to about 12 microns, more preferably between 0 and 5 microns, and most preferable less than 1 micron. In some embodiments, the impermeable layer may be a layer other than the outer layer, such as a tie layer, an intermediate layer or an inner layer. Furthermore, a substantially impermeable layer may be formed of fluorinated ethylene proplyene (FEP) which is applied, for example, as a film or dip coating. Furthermore, FEP may be electrospun with a small average pore size to create a substantially impermeable layer.
In other potential embodiments it may be desirable to create a stent with an outer layer 210 which is more porous. A porous outer layer 210 may permit healing and the integration of the prosthesis into the body. For instance, tissue of the surrounding lumen may grow into the porous outer diameter. This tissue ingrowth may permit healing at the therapy site. In some embodiments a porous outer layer 210 may be formed of electrospun PTFE.
FIG. 2B illustrates a cross sectional view of a stent with an outer layer 210, an inner layer 220, and a wire scaffold 110. Additionally, the location between the outer layer 210 and the inner layer 220 is illustrated as 230. It will be appreciated that in embodiments where there are only two layers, there may not be a gap between the two layers, but the outer layer 210 and inner layer 220 may be in direct contact where they are not separated by the wire 110.
In other embodiments a third layer may be disposed in the location 230 between the outer layer 210 and the inner layer 220. In some embodiments this layer may be a tie layer configured to promote bonding between the outer layer 210 and the inner layer 220. In other embodiments the tie layer may further be configured to provide certain properties to the stent as a whole, such as stiffness or tensile strength. Furthermore, in embodiments where both the inner layer 220 and the outer layer 210 are porous in nature, the tie layer may be configured to create an impermeable layer between the two porous layers. In such embodiments the stent may permit cell growth and healing on both the inner and outer surfaces of the stent while still preventing tissue from outside the stent from growing into the lumen and occluding the lumen.
The tie layer may consist of any thermoplastic and may or may not be electrospun. In one embodiment, the tie layer may be expanded PTFE. In another it may be electrospun PTFE. In other embodiments it may be FEP, including electrospun FEP and FEP applied as a film or dip coating. Furthermore, the tie layer may consist of any of the following polymers or any other thermoplastic, such as polyamides, polyimides, epoxies, elastomers, silicones, polyurethanes, or the like, or other melt-processable fluoropolymers, including perfluoroalkoxy (PFA), fluorinated ethylene propylene (FEP), ethylene tetrafluoroethylene (ETFE), tetrafluoroethylene hexafluoropropylene vinylidene fluoride (THV)), polyvinylidene flouride (PVDF), or ethylene chlorotrifluoroethylene (ECTFE).
Regardless of the material, the tie layer may or may not be electrospun. Further, in certain embodiments the stent may consist of two or more tie layers. The tie layer may be formed in any manner known in the art and attached to the inner and outer layers in any manner known in the art. For example, the tie layer may comprise a sheet of material which is wrapped around the inner layer 220 or a tube of material which is slipped over the inner layer 220 which is then heat shrunk or otherwise bonded to the inner and outer layers. Further, in embodiments where the tie layer is electrospun, it may be electrospun directly onto the inner layer 220, the scaffolding, or both. In some instances the tie layer may be melted after the stent is constructed to bond the tie layer to adjacent layers of the stent covering.
FIG. 3 illustrates a cross section of a stent 100 disposed within a body lumen 300. The stent includes wire scaffolding 110 and a cover 200. In embodiments where the cover 200 is composed of an outer layer and an inner layer, the outer layer may be disposed adjacent to the body lumen while the inner layer may be disposed toward the inside portion of the body lumen. In particular, in embodiments where the stent is not substantially tubular in shape, the outer cover layer may be defined as the layer disposed adjacent the body lumen wall and the inner cover layer defined as the layer disposed toward the inner portion of the body lumen.
In some embodiments, a cover 200 may be formed by electrospinning a fabric onto a spinning mandrel. In other words, the collection device may comprise a mandrel, such as a substantially cylindrical mandrel, which rotates during the electrospinning process. Varying the speed at which the mandrel rotates may influence certain properties of the fabric. For example, in some embodiments, the density of the fabric (and thereby the average pore size) may be related to the rotational speed of the mandrel. Further, the directionality of the fibers, or the degree to which the fibers are deposited in a more controlled direction or manner, may be related to the rotational speed of the mandrel. In some instances a collection mandrel may rotate at rates between about 1 RPM and about 500 RPM during the elctrospinning process, including rates from about 1 RPM to about 50 RPM or at about 25 RPM. A fabric of electrospun PTFE formed onto a spinning mandrel may thus comprise a tubular fabric having no seam and substantially isotropic properties.
Once a fabric has been electrospun onto a mandrel, the fabric may then be sintered. In the case of PTFE, the fabric may be sintered at temperatures of about 385 degrees C., including temperatures from about 360 degrees C. to about 400 degrees C. Sintering may tend to set the structure of the PTFE, meaning individual particles of PTFE are melded into continuous fibers of PTFE. The melding of the PTFE at points of contact between fibers creates a three-dimensional structure of PTFE. Furthermore, sintering may evaporate any water or PEO mixed with the PTFE, resulting in a material comprised substantially of pure PTFE.
In some embodiments, a PTFE layer may be spun onto a mandrel and then sintered. Once the fabric is sintered, the tube of material may be removed from the mandrel, then slid back on the mandrel (to initially break any adherence of the fabric to the mandrel). In other instances, low friction coatings may alternatively or additionally be applied to the mandrel before the fabric is electrospun. Once the fabric is reapplied to the mandrel, a scaffolding can be placed over the mandrel and the fabric. A second layer of material may then be spun onto the scaffolding and the fabric, and subsequently sintered. Additionally layers may also be added.
In another particular example, a first layer of PTFE may again be spun on a mandrel, sintered, removed, replaced, and a scaffolding structure applied. An FEP layer may then be applied as a film layer. An outer tube of PTFE (which may be formed separately by electrospinning onto a mandrel and sintering) may then be disposed over the FEP film layer. The entire construct may then be pressured, for example by applying a compression wrap. In some embodiments this wrap may comprise any suitable material, including a PTFE based material. In other embodiments a non-stick barrier, ie aluminum foil, may be wrapped around the construct before the compression wrap, to prevent the construct from adhering to the compression wrap.
The compressed layers may then be heated above the melting temperature of the FEP, but below the sintering temperature of the PTFE. For example, the melt temperature of the FEP may be from about 300 degrees C. to about 330 degrees C., including about 325 degrees C. PTFE may be sintered at temperatures from about 360 degrees C. to about 400 degrees C. Thus, the entire construct may be heated to an appropriate temperature such as about 325 degrees C. In some embodiments the construct may be held at this temperature for about 5 to about 10 minutes. This may allow the FEP to flow into the porous PTFE nanofiber layers surrounding the FEP. The joining of the FEP tie layer to the PTFE outer and inner cover layers may increase the strength of the finished covering. The construct may then be cooled and the compression wrap and the non-stick barrier discarded. The construct may then be removed from the mandrel.
Additionally, in some embodiments a stent may also include an extension cuff 210 (see FIG. 3) at one or both ends of the stent. The extension cuff 210 is just the coating material with no scaffold in between the inner and outer layer. The extension cuff may be present to provide easier attachment to a vessel in the body.
FIGS. 4A-5B are scanning electron micrograph (SEM) images of an exemplary embodiment of a stent covering. FIGS. 4A-4B are images of the outer layer of the covering while FIGS. 5A-5B are images of the inner layer of the covering. For each SEM, the electrospun PTFE was covered with a very thin layer of gold in order to make the structure visible on an SEM image.
FIG. 4A is an SEM image of the outer covering at 1500× (actually, 1520×) magnification, and FIG. 4B an SEM image at 3000× (actually, 2980×) magnification. Similarly, FIG. 5A is an image of the inner covering at 1500× magnification, FIG. 5B at 3000× magnification.
These SEM images reflect the microstructure of electrospun PTFE, depicting the randomly deposited criss-crossing fibers of PTFE that form the covering.
FIGS. 6A-7B are scanning electron micrograph (SEM) images of a second exemplary embodiment of a stent covering. FIGS. 6A-6B are images of the outer layer of the covering while FIGS. 7A-7B are images of the inner layer of the covering. Again, for each SEM, the electrospun PTFE was covered with a very thin layer of gold in order to make the structure visible on an SEM image.
FIG. 6A is an SEM image of the outer covering at 1500× magnification, and FIG. 6B an SEM image at 3000× (actually, 3050×) magnification. Similarly, FIG. 7A is an image of the inner covering at 1500× (actually, 1480×) magnification, and FIG. 7B at 3000× magnification.
Without further elaboration, it is believed that one skilled in the art can use the preceding description to utilize the present disclosure to its fullest extent. The examples and embodiments disclosed herein are to be construed as merely illustrative and exemplary and not a limitation of the scope of the present disclosure in any way. It will be apparent to those having skill, having the benefit of this disclosure, in the art that changes may be made to the details of the above-described embodiments without departing from the underlying principles of the disclosure herein
a scaffolding structure configured to resist radial compression when disposed in a lumen of a patient, and
a coating disposed on at least a portion of the scaffolding structure, the coating comprising a first layer of electrospun polytetrafluoroethylene (PTFE).
2. The stent of claim 1 wherein the stent further comprises a second layer of electrospun PTFE, wherein the stent is generally tubular in shape and the first layer of electrospun PTFE is disposed such that it defines an inside surface of the stent and the second layer of electrospun PTFE is disposed such that it defines an outside surface of the stent.
3. The stent of claim 2 wherein the first layer of electrospun PTFE has an average pore size of between about 2 microns and about 8 microns.
4. The stent of claim 3 wherein the first layer of electrospun PTFE has an average pore size of between about 3 microns and about 5 microns.
5. The stent of claim 2 wherein the first layer of electrospun PTFE has an average pore size configured to permit the growth of endothelial cells on the inside surface of the stent.
6. The stent of claim 2 wherein the second layer of electrospun PTFE has an average pore size of about 1 micron or less.
7. The stent of claim 2 wherein the second layer of electrospun PTFE has an average pore size configured to resist tissue growth through the outside surface of the stent.
8. The stent of claim 2 wherein a tie layer is disposed between the first layer of electrospun PTFE and the second layer of electrospun PTFE.
9. The stent of claim 8 wherein the tie layer comprises PTFE.
10. The stent of claim 8 wherein the tie layer is a thermoplastic polymer.
11. The stent of claim 1 wherein the electrospun PTFE is formed from a mixture comprising PTFE, polyethylene oxide (PEO), and water.
12. The stent of claim 11 wherein the mixture is formed by combining a PTFE dispersion with PEO dissolved in water.
13. The stent of claim 1 wherein the electrospun PTFE is electrospun onto a rotating mandrel.
14. A method of constructing a stent, comprising:
electro spinning a first tube of PTFE onto a rotating mandrel;
sintering the first tube;
applying a scaffolding structure around the first tube;
applying a fluorinated ethylene proplyene (FEP) layer around the first tube and the scaffolding structure; and
applying a second tube of electrospun PTFE around the FEP layer.
15. The method of claim 14, further comprising heat treating the stent such that the FEP layer bonds to the first and second tubes.
16. The method of claim 15 wherein the FEP partially coats fibers of the first and second tubes.
17. The method of claim 14 wherein the second tube of electrospun PTFE is formed by a method comprising:
electrospinning the second tube of PTFE onto a rotating mandrel; and sintering the second tube.
18. The method of claim 15, further comprising applying a compressive wrap around the second tube before the stent is heat treated.
19. The method of claim 14 wherein electrospinning the first tube of PTFE comprises:
20. The method of claim 14 wherein electrospinning the first tube of PTFE comprises:
discharging the mixture onto the rotating mandrel from a wire, cylinder, spike, sharp edge, or similar geometry spinning electrode that creates a perturbation.
21. A method of constructing a stent, comprising:
applying a thermoplastic polymer layer around the first tube and the scaffolding structure; and
applying a second tube of electrospun PTFE around the thermoplastic polymer layer.
22. The method of claim 21, wherein the thermoplastic polymer layer is comprised of a thermoplastic polymer selected from the group consisting of polyamides, polyimides, epoxies, elastomers, silicones, polyurethanes, or the like, or other melt-processable fluoropolymers, including perfluoroalkoxy (PFA), fluorinated ethylene propylene (FEP), ethylene tetrafluoroethylene (ETFE), tetrafluoroethylene hexafluoropropylene vinylidene fluoride (THV)), polyvinylidene flouride (PVDF), or ethylene chlorotrifluoroethylene (ECTFE).
23. The method of claim 21, further comprising heat treating the stent such that the FEP layer bonds to the first and second tubes.
US13/743,668 2009-01-16 2013-01-17 Electrospun PTFE Encapsulated Stent & Method of Manufature Abandoned US20130238086A1 (en)
US14530909P true 2009-01-16 2009-01-16
US25634909P true 2009-10-30 2009-10-30
US12/689,334 US8178030B2 (en) 2009-01-16 2010-01-19 Electrospinning of PTFE with high viscosity materials
US12/852,989 US8257640B2 (en) 2009-08-07 2010-08-09 Multilayered composite structure with electrospun layer
US12/852,993 US8262979B2 (en) 2009-08-07 2010-08-09 Process of making a prosthetic device from electrospun fibers
US201161538402P true 2011-09-23 2011-09-23
US13/272,412 US8685424B2 (en) 2010-10-14 2011-10-13 Antimicrobial substrate
US13/446,300 US20130023175A1 (en) 2009-01-16 2012-04-13 Electrospinning of ptfe with high viscosity materials
US13/564,925 US20130059497A1 (en) 2009-08-07 2012-08-02 Multilayered Composite
US13/564,927 US9034031B2 (en) 2009-08-07 2012-08-02 Prosthetic device including electrostatically spun fibrous layer and method for making the same
US13/625,548 US20130079700A1 (en) 2011-09-23 2012-09-24 Composite prosthetic shunt device
US13/743,668 US20130238086A1 (en) 2009-01-16 2013-01-17 Electrospun PTFE Encapsulated Stent & Method of Manufature
US14/631,909 US20150182668A1 (en) 2009-01-16 2015-02-26 Electrospun PTFE Encapsulated Stent & Method of Manufacture
US14/967,597 US20160296351A1 (en) 2009-01-16 2015-12-14 Electrospun ptfe encapsulated stent and method of manufacture
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US13/564,925 Continuation-In-Part US20130059497A1 (en) 2009-08-07 2012-08-02 Multilayered Composite
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US14/967,597 Continuation US20160296351A1 (en) 2009-01-16 2015-12-14 Electrospun ptfe encapsulated stent and method of manufacture
US20130238086A1 true US20130238086A1 (en) 2013-09-12
ID=49114783
US13/743,668 Abandoned US20130238086A1 (en) 2009-01-16 2013-01-17 Electrospun PTFE Encapsulated Stent & Method of Manufature
US14/631,909 Abandoned US20150182668A1 (en) 2009-01-16 2015-02-26 Electrospun PTFE Encapsulated Stent & Method of Manufacture
US14/967,597 Abandoned US20160296351A1 (en) 2009-01-16 2015-12-14 Electrospun ptfe encapsulated stent and method of manufacture
US (3) US20130238086A1 (en)
CN103611189A (en) * 2013-11-21 2014-03-05 无锡中科光远生物材料有限公司 Bacteriostatic composition, implant material and preparation method thereof
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2013-01-17 US US13/743,668 patent/US20130238086A1/en not_active Abandoned
2015-02-26 US US14/631,909 patent/US20150182668A1/en not_active Abandoned
2015-12-14 US US14/967,597 patent/US20160296351A1/en not_active Abandoned
US20150182668A1 (en) 2015-07-02
US20160296351A1 (en) 2016-10-13
EP2149349B1 (en) 2019-04-24 Prosthetic valve
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Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:BALLARD, ROBERT L.;ANNEAUX, BRUCE L.;PUCKETT, SABRINA D.;AND OTHERS;REEL/FRAME:029931/0865