WO2002049678A2 - Method and apparatus for manufacturing polymer fiber shells via electrospinning - Google Patents

Method and apparatus for manufacturing polymer fiber shells via electrospinning Download PDF

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Publication number
WO2002049678A2
WO2002049678A2 PCT/IL2001/001168 IL0101168W WO0249678A2 WO 2002049678 A2 WO2002049678 A2 WO 2002049678A2 IL 0101168 W IL0101168 W IL 0101168W WO 0249678 A2 WO0249678 A2 WO 0249678A2
Authority
WO
WIPO (PCT)
Prior art keywords
electrode
precipitation electrode
precipitation
subsidiary
polymer
Prior art date
Application number
PCT/IL2001/001168
Other languages
French (fr)
Other versions
WO2002049678A3 (en
WO2002049678A8 (en
Inventor
Alexander Dubson
Eli Bar
Original Assignee
Nicast Ltd.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority to EP01271232A priority Critical patent/EP1355677B1/en
Priority to AU2002216340A priority patent/AU2002216340A1/en
Priority to MXPA03005551A priority patent/MXPA03005551A/en
Priority to US10/433,621 priority patent/US7112293B2/en
Priority to JP2002551015A priority patent/JP2005507464A/en
Priority to IL15651301A priority patent/IL156513A0/en
Priority to DE60141607T priority patent/DE60141607D1/en
Priority to CA002432156A priority patent/CA2432156A1/en
Application filed by Nicast Ltd. filed Critical Nicast Ltd.
Priority to AT01271232T priority patent/ATE460903T1/en
Publication of WO2002049678A2 publication Critical patent/WO2002049678A2/en
Publication of WO2002049678A8 publication Critical patent/WO2002049678A8/en
Publication of WO2002049678A3 publication Critical patent/WO2002049678A3/en
Priority to IL156513A priority patent/IL156513A/en
Priority to US11/398,573 priority patent/US20070031607A1/en

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Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/04Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06Blood vessels
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/507Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials for artificial blood vessels
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/56Porous materials, e.g. foams or sponges
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B29WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
    • B29CSHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
    • B29C67/00Shaping techniques not covered by groups B29C39/00 - B29C65/00, B29C70/00 or B29C73/00
    • B29C67/20Shaping techniques not covered by groups B29C39/00 - B29C65/00, B29C70/00 or B29C73/00 for porous or cellular articles, e.g. of foam plastics, coarse-pored
    • DTEXTILES; PAPER
    • D01NATURAL OR MAN-MADE THREADS OR FIBRES; SPINNING
    • D01DMECHANICAL METHODS OR APPARATUS IN THE MANUFACTURE OF ARTIFICIAL FILAMENTS, THREADS, FIBRES, BRISTLES OR RIBBONS
    • D01D5/00Formation of filaments, threads, or the like
    • D01D5/0007Electro-spinning
    • DTEXTILES; PAPER
    • D01NATURAL OR MAN-MADE THREADS OR FIBRES; SPINNING
    • D01DMECHANICAL METHODS OR APPARATUS IN THE MANUFACTURE OF ARTIFICIAL FILAMENTS, THREADS, FIBRES, BRISTLES OR RIBBONS
    • D01D5/00Formation of filaments, threads, or the like
    • D01D5/0007Electro-spinning
    • D01D5/0061Electro-spinning characterised by the electro-spinning apparatus
    • D01D5/0069Electro-spinning characterised by the electro-spinning apparatus characterised by the spinning section, e.g. capillary tube, protrusion or pin
    • DTEXTILES; PAPER
    • D01NATURAL OR MAN-MADE THREADS OR FIBRES; SPINNING
    • D01DMECHANICAL METHODS OR APPARATUS IN THE MANUFACTURE OF ARTIFICIAL FILAMENTS, THREADS, FIBRES, BRISTLES OR RIBBONS
    • D01D5/00Formation of filaments, threads, or the like
    • D01D5/0007Electro-spinning
    • D01D5/0061Electro-spinning characterised by the electro-spinning apparatus
    • D01D5/0092Electro-spinning characterised by the electro-spinning apparatus characterised by the electrical field, e.g. combined with a magnetic fields, using biased or alternating fields
    • DTEXTILES; PAPER
    • D01NATURAL OR MAN-MADE THREADS OR FIBRES; SPINNING
    • D01DMECHANICAL METHODS OR APPARATUS IN THE MANUFACTURE OF ARTIFICIAL FILAMENTS, THREADS, FIBRES, BRISTLES OR RIBBONS
    • D01D5/00Formation of filaments, threads, or the like
    • D01D5/18Formation of filaments, threads, or the like by means of rotating spinnerets
    • DTEXTILES; PAPER
    • D04BRAIDING; LACE-MAKING; KNITTING; TRIMMINGS; NON-WOVEN FABRICS
    • D04HMAKING TEXTILE FABRICS, e.g. FROM FIBRES OR FILAMENTARY MATERIAL; FABRICS MADE BY SUCH PROCESSES OR APPARATUS, e.g. FELTS, NON-WOVEN FABRICS; COTTON-WOOL; WADDING ; NON-WOVEN FABRICS FROM STAPLE FIBRES, FILAMENTS OR YARNS, BONDED WITH AT LEAST ONE WEB-LIKE MATERIAL DURING THEIR CONSOLIDATION
    • D04H1/00Non-woven fabrics formed wholly or mainly of staple fibres or like relatively short fibres
    • D04H1/70Non-woven fabrics formed wholly or mainly of staple fibres or like relatively short fibres characterised by the method of forming fleeces or layers, e.g. reorientation of fibres
    • D04H1/72Non-woven fabrics formed wholly or mainly of staple fibres or like relatively short fibres characterised by the method of forming fleeces or layers, e.g. reorientation of fibres the fibres being randomly arranged
    • D04H1/728Non-woven fabrics formed wholly or mainly of staple fibres or like relatively short fibres characterised by the method of forming fleeces or layers, e.g. reorientation of fibres the fibres being randomly arranged by electro-spinning
    • DTEXTILES; PAPER
    • D04BRAIDING; LACE-MAKING; KNITTING; TRIMMINGS; NON-WOVEN FABRICS
    • D04HMAKING TEXTILE FABRICS, e.g. FROM FIBRES OR FILAMENTARY MATERIAL; FABRICS MADE BY SUCH PROCESSES OR APPARATUS, e.g. FELTS, NON-WOVEN FABRICS; COTTON-WOOL; WADDING ; NON-WOVEN FABRICS FROM STAPLE FIBRES, FILAMENTS OR YARNS, BONDED WITH AT LEAST ONE WEB-LIKE MATERIAL DURING THEIR CONSOLIDATION
    • D04H3/00Non-woven fabrics formed wholly or mainly of yarns or like filamentary material of substantial length
    • D04H3/02Non-woven fabrics formed wholly or mainly of yarns or like filamentary material of substantial length characterised by the method of forming fleeces or layers, e.g. reorientation of yarns or filaments
    • D04H3/07Non-woven fabrics formed wholly or mainly of yarns or like filamentary material of substantial length characterised by the method of forming fleeces or layers, e.g. reorientation of yarns or filaments otherwise than in a plane, e.g. in a tubular way
    • DTEXTILES; PAPER
    • D04BRAIDING; LACE-MAKING; KNITTING; TRIMMINGS; NON-WOVEN FABRICS
    • D04HMAKING TEXTILE FABRICS, e.g. FROM FIBRES OR FILAMENTARY MATERIAL; FABRICS MADE BY SUCH PROCESSES OR APPARATUS, e.g. FELTS, NON-WOVEN FABRICS; COTTON-WOOL; WADDING ; NON-WOVEN FABRICS FROM STAPLE FIBRES, FILAMENTS OR YARNS, BONDED WITH AT LEAST ONE WEB-LIKE MATERIAL DURING THEIR CONSOLIDATION
    • D04H3/00Non-woven fabrics formed wholly or mainly of yarns or like filamentary material of substantial length
    • D04H3/08Non-woven fabrics formed wholly or mainly of yarns or like filamentary material of substantial length characterised by the method of strengthening or consolidating
    • D04H3/16Non-woven fabrics formed wholly or mainly of yarns or like filamentary material of substantial length characterised by the method of strengthening or consolidating with bonds between thermoplastic filaments produced in association with filament formation, e.g. immediately following extrusion
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/04Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06Blood vessels
    • A61F2/07Stent-grafts
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/04Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06Blood vessels
    • A61F2/07Stent-grafts
    • A61F2002/072Encapsulated stents, e.g. wire or whole stent embedded in lining
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2210/00Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0076Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof multilayered, e.g. laminated structures
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0014Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
    • A61F2250/0023Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in porosity
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0058Additional features; Implant or prostheses properties not otherwise provided for
    • A61F2250/0067Means for introducing or releasing pharmaceutical products into the body
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T428/00Stock material or miscellaneous articles
    • Y10T428/13Hollow or container type article [e.g., tube, vase, etc.]
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T428/00Stock material or miscellaneous articles
    • Y10T428/13Hollow or container type article [e.g., tube, vase, etc.]
    • Y10T428/1352Polymer or resin containing [i.e., natural or synthetic]
    • Y10T428/1372Randomly noninterengaged or randomly contacting fibers, filaments, particles, or flakes
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T428/00Stock material or miscellaneous articles
    • Y10T428/13Hollow or container type article [e.g., tube, vase, etc.]
    • Y10T428/1352Polymer or resin containing [i.e., natural or synthetic]
    • Y10T428/139Open-ended, self-supporting conduit, cylinder, or tube-type article
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T428/00Stock material or miscellaneous articles
    • Y10T428/13Hollow or container type article [e.g., tube, vase, etc.]
    • Y10T428/1352Polymer or resin containing [i.e., natural or synthetic]
    • Y10T428/139Open-ended, self-supporting conduit, cylinder, or tube-type article
    • Y10T428/1393Multilayer [continuous layer]
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T442/00Fabric [woven, knitted, or nonwoven textile or cloth, etc.]
    • Y10T442/60Nonwoven fabric [i.e., nonwoven strand or fiber material]
    • Y10T442/608Including strand or fiber material which is of specific structural definition
    • Y10T442/614Strand or fiber material specified as having microdimensions [i.e., microfiber]

Definitions

  • the present invention relates to a method and apparatus for manufacturing polymer fiber shells via electrospinning.
  • Polymer fiber shells such as tubular shaped products, are used in the medical industry for various utilities including esophageal grafts, vascular grafts, stent coats and like. Numerous methods for manufacturing polymer fiber shells suitable for medical applications are known in the art, including, for example, various injection molding methods, mandrel assisted extrusion or formation and various weaving techniques.
  • Vascular grafts known in the art typically have a microporous structure that in general allows tissue growth and cell endothelization, thus contributing to long term engraftment and patency of the graft.
  • tissue ingrowth and cell endothelization is typically enhanced with increased in grafts exhibiting increased porosity.
  • increasing the porosity of vascular grafts leads to a considerable reduction of the mechanical and tensile strength of the graft, and as a consequence to a reduction in the functionality thereof.
  • Electrospinning has been used for generating various products for medical applications, e.g., wound dressings, prosthetic devices, and vascular grafts as well as for industrial use, e.g., electrolytic cell diaphragms, battery separators, and fuel cell components ⁇ It has already been proposed to produce by electrospinning products having the appearance of shells.
  • U.S. Patent No. 4,323,525 discloses a method of preparing a tubular product by electrostatically spinning a fiber forming material and collecting the resulting spun fibers on a rotating mandrel.
  • U.S. Patent No. 4,552,707 discloses a varying rotation rate mandrel which controls the "anisotropy extent" of fiber orientation of the final product. Additional examples of tubular shaped products and a like • are disclosed, e.g., in U.S. Patent Nos. 4,043,331, 4,127,706, 4,143,196, 4,223,101, 4,230,650 and 4,345,414.
  • the process of electrospinning creates a fine stream or jet of liquid that upon proper evaporation yields a non-woven fiber structure.
  • the fine stream of liquid is produced by pulling a small amount of a liquefied polymer (either polymer dissolved in solvent (polymer solution) or melted polymer) through space using electrical forces.
  • the produced fibers are then collected on a suitably located precipitation device, such as a mandrel to form tubular structures.
  • a precipitation device such as a mandrel to form tubular structures.
  • the hardening procedure may be mere cooling, however other procedures such as chemical hardening or evaporation of solvent may also be employed.
  • an electric field with high filed lines density may results in a corona discharge near the precipitation device, and consequently prevent fibers from being collected by the precipitation device.
  • the filed lines density of an electric field is determined inter alia by the geometry of the precipitation device; in particular, sharp edges on the precipitation device increase the effect of corona discharge.
  • products with at least a section with a small radius of curvature are coated coaxially by the fibers.
  • Such structural fiber formation considerably reduces the radial tensile strength of a spun product, which, in the case of vascular grafts, is necessary for withstanding pressures generated by blood flow.
  • an apparatus for manufacturing polymer fiber shells from liquefied polymer comprising: (a) a precipitation electrode being for generating the polymer fiber shell thereupon; (b) a dispenser, being at a first potential relative to the precipitation electrode so as to generate an electric field between the precipitation electrode and the dispenser, the dispenser being for: (i) charging the liquefied polymer thereby providing a charged liquefied polymer; and (ii) dispensing the charged liquefied polymer in a direction of the precipitation electrode; and (c) a subsidiary electrode being at a second potential relative to the precipitation electrode, the subsidiary electrode being for modifying the electric field between the precipitation electrode and the dispenser.
  • a method for forming a liquefied polymer into a non-woven polymer fiber shells comprising: (a) charging the liquefied polymer thereby producing a charged liquefied polymer; (b) subjecting the charged liquefied polymer to a first electric field; (c) dispensing the charged liquefied polymer within the first electric field in a direction of a precipitation electrode, the precipitation electrode being designed and configured for generating the polymer fiber shell; (d) providing a second electric field being for modifying the first electric field; and (e) using the precipitation electrode to collect the charged liquefied polymer thereupon, thereby forming the non-woven polymer fiber shell.
  • the first electric field is defined between the precipitation electrode and a dispensing electrode being at a first potential relative to the precipitation electrode.
  • step (c) is effected by dispensing the charged liquefied polymer from the dispensing electrode.
  • the second electric field is defined by a subsidiary electrode being at a second potential relative to the precipitation electrode.
  • the subsidiary electrode serves for controlling fiber orientation of the polymer fiber shell generated upon the precipitation electrode. According to still further features in the described preferred embodiments the subsidiary electrode serves to minimize a volume charge generated between the dispenser and the precipitation electrode.
  • the method further comprising moving the subsidiary electrode along the precipitation electrode during step (e).
  • the method further comprising moving the dispensing electrode along the precipitation electrode during step (c).
  • the method further comprising synchronizing the motion of the dispensing electrode and the subsidiary electrode along the precipitation electrode.
  • the dispenser comprises a mechanism for forming a jet of the charged liquefied polymer.
  • the apparatus further comprising a bath for holding the liquefied polymer.
  • the mechanism for forming a jet of the charged liquefied polymer includes a dispensing electrode.
  • the dispenser is operative to move along a length of the precipitation electrode.
  • the precipitation electrode includes at least one rotating mandrel.
  • the rotating mandrel is a cylindrical mandrel. According to still further features in the described preferred embodiments the rotating mandrel is an intricate-profile mandrel.
  • the intricate-profile mandrel includes sharp structural elements.
  • the cylindrical mandrel is of a diameter selected from a range of 0.1 to 20 millimeters.
  • the precipitation electrode includes at least one structural element selected from the group consisting of a protrusion, an orifice, a groove, and a grind.
  • the subsidiary electrode is of a shape selected from the group consisting of a plane, a cylinder, a torus and a wire.
  • the subsidiary electrode is operative to move along a length of the precipitation electrode.
  • the subsidiary electrode is tilted at angle with respect to a longitudinal axis of the precipitation electrode, the angle is ranging between 45 and 90 degrees.
  • the subsidiary electrode is positioned at a distance of 5 - 70 millimeters from the precipitation electrode.
  • the subsidiary electrode is positioned at a distance ⁇ from the precipitation electrode, ⁇ being equal to 12 ⁇ R(l-V 2 /N ⁇ ), where ⁇ is a constant ranging between about 0.7 and about 0.9, R is the curvature-radius of the polymer fiber shell formed on the precipitation electrode, Vi is the first potential and V 2 is the second potential.
  • an apparatus for manufacturing a polymer fiber shells from liquefied polymer comprising: (a) a dispenser, for: (i) charging the liquefied polymer thereby providing a charged liquefied polymer; and (ii) dispensing the charged liquefied polymer; and (b) a precipitation electrode being at a potential relative to the dispenser thereby generating an electric field between the precipitation electrode and the dispenser, the precipitation electrode being for collecting the charged liquefied polymer drawn by the electric field, to thereby form the polymer fiber shell thereupon, wherein the precipitation electrode is designed so as to reduce non-uniformities in the electric field.
  • the precipitation electrode is formed from a combination of electroconductive and non-electroconductive materials.
  • a surface of the precipitation electrode is formed by a predetermined pattern of the electroconductive and non-electroconductive materials.
  • the precipitation electrode is formed from at least two layers.
  • the at least two layers include an electroconductive layer and a partial electroconductive layer.
  • the partial electroconductive layer is partial electroconductive layer is formed from a combination of an electroconductive material and at least one dielectric material.
  • the dielectric material is selected from a group consisting of polyamide and polyacrylonitrile and polytetrafluoroethylene.
  • the dielectric material is Titanium Nitride.
  • the partial electroconductive layer is selected of a thickness ranging between 0.1 to 90 microns.
  • the present invention successfully addresses the shortcomings of the presently known configurations by providing an electrospinning apparatus and method capable of fabricating a non-woven polymer fiber shell which can be used in vascular grafts.
  • FIG. 1 is a schematic illustration of a prior art electrospinning apparatus
  • FIG. 2 is a schematic illustration of an electrospinning apparatus which includes a subsidiary electrode according to the teachings of the present invention
  • FIG. 3 is a schematic illustration of an electrospinning apparatus which includes a planar subsidiary electrode according to the teachings of the present invention
  • FIG. 4 is a schematic illustration of an electrospinning apparatus which includes a cylindrical subsidiary electrode according to the teachings of the present invention
  • FIG. 5 is a schematic illustration of an electrospinning apparatus which includes a linear subsidiary electrode according to the teachings of the present invention
  • FIG. 6 is a schematic illustration of an electrospinning apparatus which includes a composite subsidiary electrode according to the teachings of the present invention.
  • FIG. 7 is an electron microscope image of material spun using conventional electrospinning techniques
  • FIG. 8 is an electron microscope image of material spun using an apparatus which incorporates a flat subsidiary electrode, positioned 20 millimeters from the mandrel, according to the teachings of the present invention
  • FIG. 9 is an electron microscope image of material spun using an apparatus which incorporates a flat subsidiary electrode, positioned 9 millimeters from the mandrel, according to the teachings of the present invention.
  • FIG. 10 is an electron microscope image of polar-oriented material spun using an apparatus which incorporates a linear subsidiary electrode according to the teachings of the present invention. DESCRIPTION OF THE PREFERRED EMBODIMENTS
  • the present invention is of a method and an apparatus for manufacturing a polymer fiber shell using electrospinning. Specifically, the present invention can be used to manufacture intricate-profile products and vascular grafts of small to large diameter via electrospinning.
  • Figure 1 illustrates an apparatus for manufacturing a tubular structure using a conventional electrospinning apparatus, which is referred to herein as apparatus 10.
  • Apparatus 10 includes a dispenser 12 which can be, for example, a bath provided with capillary apertures 14.
  • Dispenser 12 serves for storing the polymer to be spun in a liquid form.
  • Dispenser 12 is positioned at a predetermined distance from a precipitation electrode 16.
  • Precipitation electrode 16 serves for generating the tubular structure thereupon.
  • Precipitation electrode 16 is typically manufactured in the form of a mandrel or any other cylindrical structure.
  • Precipitation electrode 16 is rotated by a mechanism such that a tubular structure is formed when coated with the polymer.
  • Dispenser 12 is typically grounded, while precipitation electrode 16 is connected to a source of high voltage preferably of negative polarity, thus forming an electric field between dispenser 12 and precipitation electrode 16.
  • precipitation electrode 16 can be grounded while dispenser 12 is connected to a source of high voltage, preferably with positive polarity.
  • a liquefied polymer e.g., melted polymer or dissolved polymer
  • a process of solvent evaporation or cooling starts which is accompanied by the creation of capsules with a semi-rigid envelope or crust.
  • An electric field occasionally accompanied a by unipolar corona discharge in the area of dispenser 12, is generated by the potential difference between dispenser 12 and precipitation electrode 16. Because the liquefied polymer possesses a certain degree of electrical conductivity, the above-described capsules become charged.
  • the charges tend to distribute along the jets, thus preventing existence of any non-zero component of electric field inside the jet.
  • a conduction current flows along the jets, which results in the accumulation of (different sign) free charges on the liquefied polymer surface.
  • the jets depart from the dispenser 12 and travel towards the opposite polarity electrode, i.e., precipitation electrode 16.
  • the jet cools or solvent therein evaporates, thus forming fibers which are collected on the surface of precipitation electrode 16. Since electrode 16 is rotating the charged fibers form a tubular shape.
  • the orientation of the electric field maximal strength vector is such that precipitation electrode 16 is coated coaxially by the fibers.
  • small diameter products have limited radial strength when manufactured via existing electrospinning methods, as described above.
  • the electric field magnitude in the vicinity of precipitation electrode 16 may exceed the air electric strength (about 30 kV/cm), and a corona discharge may develop in the area of precipitation electrode 16.
  • the effect of corona discharge decreases the coating efficiency of the process as described hereinbelow, and may even resultant in a total inability of fibers to be collected upon precipitation electrode 16.
  • Corona discharge initiation is accompanied by the generation of a considerable amount of air ions having opposite charge sign with respect to the charged fibers.
  • apparatus 20 includes a precipitation electrode
  • Precipitation electrode 22 can be, for example, a mandrel of uniform or varying radius, which may include some structural elements such as, but not limited to, protrusions, orifices and grooves.
  • the surface of precipitation electrode 22 may also contain grinds.
  • the diameter of the mandrel may vary from about 0.1 millimeter up to about 20 millimeters depending on the diameter of the polymer fiber shell to be spun thereupon.
  • Apparatus 20 further includes a dispenser 24, which is at a first potential relative to precipitation electrode 22. Such a potential can be generated by grounding dispenser 24, and connecting a source of high voltage with negative polarity to precipitation electrode 22.
  • precipitation electrode 22 can be grounded while dispenser 24 is connected to a source of high voltage with positive polarity.
  • an absolute value for the potential difference between dispenser 24 and precipitation electrode 22 may range between about 10 kV and about 100 kV.
  • Dispenser 24 serves for charging the liquefied polymer, thereby providing a charged liquefied polymer and dispensing the charged liquefied polymer in a direction of precipitation electrode 22.
  • Dispenser 24 may also include a mechanism for moving it along a longitudinal axis of precipitation electrode 22, thus enabling dispensing of the charged liquefied polymer at various points along the longitudinal axis of precipitation electrode 22.
  • the charged liquefied polymer may be, for example polyurethane, polyester, polyolefin, polymethyl methacrylate, polyvinyl aromatic, polyvinyl ester, polyamide, polyimide, polyether, polycarbonate, polyacrilonitrile, polyvinyl pyrrolidone, polyethylene oxide, poly (L-lactic acid), poly (lactide-CD-glycoside), polycaprolactone, polyphosphate ester, poly (gly colic acid), poly (DL-lactic acid), and some copolymers.
  • Biolmolecules such as DNA, silk, chitozan and cellulose may also be used. Improved charging of the polymer may also be required.
  • Improved charging is effected according to the present invention by mixing the liquefied polymer with a charge control agent (e.g., a dipolar additive) to form, for example, a polymer-dipolar additive complex which apparently better interacts with ionized air molecules formed under the influence of the electric field.
  • a charge control agent e.g., a dipolar additive
  • the charge control agent is typically added in the grams equivalent per liter range, say, in the range of from about 0.001 N to about 0.1 N, depending on the respective molecular weights of the polymer and the charge control agent used.
  • U.S. Pat. Nos. 5,726,107; 5,554,722; and 5,558,809 teach the use of charge control agents in combination with polycondensation processes in the production of electret fibers, which are fibers characterized in a permanent electric charge, using melt spinning and other processes devoid of the use of an precipitation electrode.
  • a charge control agent is added in such a way that it is incorporated into the melted or partially melted fibers and remains incorporated therein to provide the fibers with electrostatic charge which is not dissipating for prolonged time periods, say months.
  • the charge control agent transiently binds to the outer surface of the fibers and therefore the charge dissipates shortly thereafter (within minutes). This is because polycondensation is not exercised at all such the chemical intereaction between the agent and the polymer is absent, and further due to the low concentration of charge control agent employed. The resulting shell is therefore substantially charge free.
  • dispenser 24 typically includes a bath for holding the liquefied polymer and a mechanism for forming a jet, which mechanism may be, for example, a dispensing electrode.
  • Apparatus 20 further includes at least one subsidiary electrode 26 which is at a second potential relative to precipitation electrode 22.
  • Subsidiary electrode 26 serves for controlling the direction and magnitude of the electric field between precipitation electrode 22 and dispenser 24 and as such, subsidiary electrode 26 can be used to control the orientation of polymer fibers deposited on precipitation electrode 22.
  • subsidiary electrode 26 serves as a supplementary screening electrode. Broadly stated, use of screening results in decreasing the coating precipitation factor, which is particularly important upon mandrels having at least a section of small radii of curvature.
  • the size, shape, position and number of subsidiary electrode 26 is selected so as to maximize the coating precipitation factor, while minimizing the effect of corona discharge in the area of precipitation electrode 22 and/or so as to provide for controlled fiber orientation upon deposition.
  • subsidiary electrode 26 is positioned 5-70 mm away from precipitation electrode 22.
  • such a distance is selected according to the following:
  • Subsidiary electrode 26 may include a mechanism for moving it along a longitudinal axis of precipitation electrode 22. Such a mechanism may be in use when enhanced control over fiber orientation is required.
  • Subsidiary electrode 26 may also be tilted through an angle of 45-90 degrees with respect to the longitudinal axis of precipitation electrode 22. Such tilting may be used to provide for controlled fiber orientation upon deposition, hence to control the radial strength of the manufactured shell; specifically, large angles result in higher radial strength.
  • the shape and size of electrode 26 may also determine the quality of the shell formed by apparatus 20.
  • electrode 26 may be fabricated in a variety of shapes each serving a specific purpose. Electrode shapes which can be used with apparatus 20 of the present invention include, but are not limited to, a plane, a cylinder, a torus a rod, a knife, an arc or a ring.
  • An apparatus 20 which includes a subsidiary electrode 26 of a cylindrical ( Figure 4) or a flat shape ( Figure 3) enables manufacturing intricate-profile products being at least partially with small radius of curvature, which radius may range between 0.025 millimeters and 5 millimeters.
  • the coating of such structures is characterized by random-oriented (Figure 8) or even polar-oriented ( Figure 9) fibers, as opposed to an axial coating which is typical for small curvature products manufactured via existing electrospinning methods as demonstrated in Figure 7 (further described in the Examples section).
  • 26 and precipitation electrode 22 can be determined as ⁇ /x where x is a factor ranging between 1.8 and 2, and where ⁇ is as defined by Equation 1 above.
  • positioning and/or shape of electrode 26 determines fiber orientation in the polymer fiber shell formed.
  • control fiber orientation is important when fabricating vascular grafts in which a high radial strength and elasticity is important. It will be appreciated that a polar oriented structure can generally be obtained also by wet spinning methods, however in wet spinning methods the fibers are thicker than those used by electrospinning by at least an order of magnitude. Control over fiber orientation is also advantageous when fabricating composite polymer fiber shells which are manufactured by sequential deposition of several different fiber materials.
  • Figure 5 illustrates an apparatus 20 which utilizes a linear (e.g., a rod, a knife, an arc or a ring) subsidiary electrode 26.
  • a linear e.g., a rod, a knife, an arc or a ring
  • subsidiary electrode 26 of linear shape is based on the distortion it introduces to the electric field in an area adjacent to precipitation electrode 22.
  • the diameter of subsidiary electrode 26 must be considerably smaller than that of precipitation electrode 22, yet large enough to avoid generation of a significant corona discharge.
  • Fiber coating generated by apparatus 20 utilizing a linear subsidiary electrode 26 is illustrated by Figure 10 which is further described in the Examples section hereinunder.
  • the present invention provides an electrospinning apparatus in which the electric field is under substantial control, thereby providing either random or predetermined fibers orientation.
  • precipitation electrode 34 of apparatus 30 having a dispenser 32 can be designed and configured so as to reduce non-uniformities in the electric field.
  • precipitation electrode 34 is fabricated from at least two layers of materials, an inner layer 36 made of electroconductive material and an outer layer 38 made of a material having high dielectric properties. Such a fabrication design results in a considerable increase of corona discharge threshold thus considerably reducing corona discharge from precipitation electrode 34.
  • Materials suitable for use with outer layer 38 of precipitation electrode 34 can be ceramic materials e.g., Titanium Nitride, Aluminum
  • outer layer 38 depends on the dielectric properties of the material from which it is made and can vary from less than one micron, in the case of, for example, a
  • Titanium Nitride layer or tens of microns, in the case of, for example, polytetrafluoroethylene, polyamide or polyacrylonitrile layer.
  • this precipitation electrode configuration enables easier separation of formed structures therefrom.
  • outer layer 38 of precipitation electrode 34 can also be configured for facilitating the removal of the final product from the mandrel.
  • a polycarbonate resin grade Caliper 2071 was purchased from Daw Chemical Co. This Polymer is characterized as having good fiber forming abilities and is convenient for electrospinning. Chloroform was used as solvent in all of the examples described hereinbelow.
  • Figure 7 is an example of non-randomized covering of thin mandrels via conventional electrospinning.
  • a 3-mm cylindrical mandrel was covered by polycarbonate fiber using prior art electrospinning approaches.
  • Figure 7 is an electron microscope image of the final product, in which axial fiber orientation is well evident. Due to non-uniformities in the electric field, the fibers, while still in motion in the inter-electrode space, are oriented in conformity with the field configuration, and the obtained tubular structure exhibits axial orientation of fibers, and as such is characterized by axial, as opposed to radial strength.
  • EXAMPLE 3 Polar-Oriented Covering Using Flat Subsidiary electrode
  • An apparatus constructed and operative in accordance with the teachings of the present invention incorporating a flat subsidiary electrode positioned 9 millimeters from the mandrel and being at a potential difference of 5 kV from the mandrel was used to spin a polycarbonate tubular structure of a 3 mm radius.
  • EXAMPLE 4 Predefined Oriented Covering Using Linear Subsidiary electrode
  • Figure 10 illustrates result obtained from an apparatus configuration which may be employed in order to obtain a predefined oriented structural fiber covering.
  • An apparatus which includes an elliptical subsidiary electrode and a dispenser both moving along the longitudinal axis of the mandrel in a reciprocating synchronous movement was used to coat a 3-mm cylindrical mandrel with polycarbonate fiber.
  • the subsidiary electrode had a large diameter of 120 mm, a small diameter of 117.6 mm and a thickness of 1.2 mm.
  • the subsidiary electrode was positioned 15 mm from the mandrel, at an 80 ° tilt with respect to the mandrel symmetry axis. It is appreciated that certain features of the invention, which are, for clarity, described in the context of separate embodiments, may also be provided in combination in a single embodiment.

Abstract

An apparatus for manufacturing a polymer fiber shell from liquefied polymer is provided. The apparatus includes: (a) a precipitation electrode being for generating the polymer fiber shell thereupon; (b) a dispenser, being at a first potential relative to the precipitation electrode so as to generate an electric field between the precipitation electrode and the dispenser, the dispenser being for: (i) charging the liquefied polymer thereby providing a charged liquefied polymer; and (ii) dispensing the charged liquefied polymer in a direction of the precipitation electrode; and (c) a subsidiary electrode being at a second potential relative to the precipitation electrode, the subsidiary electrode being for modifying the electric field between the precipitation electrode and the dispenser.

Description

METHOD AND APPARATUS FOR MANUFACTURING POLYMER FIBER SHELLS VIA ELECTROSPINNING
FIELD AND BACKGROUND OF THE INVENTION The present invention relates to a method and apparatus for manufacturing polymer fiber shells via electrospinning.
Polymer fiber shells such as tubular shaped products, are used in the medical industry for various utilities including esophageal grafts, vascular grafts, stent coats and like. Numerous methods for manufacturing polymer fiber shells suitable for medical applications are known in the art, including, for example, various injection molding methods, mandrel assisted extrusion or formation and various weaving techniques.
Production of polymer fiber shells suitable for use as vascular grafts - is particularly difficult, since such grafts must withstand high and pulsatile blood pressures while, at the same time, be elastic and biocompatible.
Vascular grafts known in the art typically have a microporous structure that in general allows tissue growth and cell endothelization, thus contributing to long term engraftment and patency of the graft. In vascular grafts, tissue ingrowth and cell endothelization is typically enhanced with increased in grafts exhibiting increased porosity. However, increasing the porosity of vascular grafts leads to a considerable reduction of the mechanical and tensile strength of the graft, and as a consequence to a reduction in the functionality thereof. Electrospinning has been used for generating various products for medical applications, e.g., wound dressings, prosthetic devices, and vascular grafts as well as for industrial use, e.g., electrolytic cell diaphragms, battery separators, and fuel cell components^ It has already been proposed to produce by electrospinning products having the appearance of shells. For example, U.S. Patent No. 4,323,525 discloses a method of preparing a tubular product by electrostatically spinning a fiber forming material and collecting the resulting spun fibers on a rotating mandrel. U.S. Patent No. 4,552,707 discloses a varying rotation rate mandrel which controls the "anisotropy extent" of fiber orientation of the final product. Additional examples of tubular shaped products and a like • are disclosed, e.g., in U.S. Patent Nos. 4,043,331, 4,127,706, 4,143,196, 4,223,101, 4,230,650 and 4,345,414.
The process of electrospinning creates a fine stream or jet of liquid that upon proper evaporation yields a non-woven fiber structure. The fine stream of liquid is produced by pulling a small amount of a liquefied polymer (either polymer dissolved in solvent (polymer solution) or melted polymer) through space using electrical forces. The produced fibers are then collected on a suitably located precipitation device, such as a mandrel to form tubular structures. In the case of a melted polymer which is normally solid at room temperature, the hardening procedure may be mere cooling, however other procedures such as chemical hardening or evaporation of solvent may also be employed.
In electrospinning, an electric field with high filed lines density (i.e., having large magnitude per unit volume) may results in a corona discharge near the precipitation device, and consequently prevent fibers from being collected by the precipitation device. The filed lines density of an electric field is determined inter alia by the geometry of the precipitation device; in particular, sharp edges on the precipitation device increase the effect of corona discharge. In addition, due to the effect of electric dipole rotation along the electric field maximal strength vector in the vicinity of the mandrel, products with at least a section with a small radius of curvature are coated coaxially by the fibers. Such structural fiber formation considerably reduces the radial tensile strength of a spun product, which, in the case of vascular grafts, is necessary for withstanding pressures generated by blood flow.
Various electrospinning based manufacturing methods for generating vascular grafts are known in the prior art, see, for example, U.S. Patent Nos. 4,044,404, 4,323,525, 4,738,740, 4,743,252, and 5,575,818. However, such methods suffer from the above inherent limitations which limit the use thereof when generating intricate profile fiber shells.
Hence, although electrospinning can be efficiently used for generating large diameter shells, the nature of the electrospinning process prevents efficient generation of products having an intricate profile and/or small diameter, such as vascular grafts. In particular, since porosity and radial strength are conflicting, prior art electrospinning methods cannot be effectively used for manufacturing vascular grafts having both characteristics. There is thus a widely recognized need for, and it would be highly advantageous to have, a method and apparatus for manufacturing polymer fiber shells via electrospinning devoid of the above limitations.
SUMMARY OF THE INVENTION According to one aspect of the present invention there is provided an apparatus for manufacturing polymer fiber shells from liquefied polymer, the apparatus comprising: (a) a precipitation electrode being for generating the polymer fiber shell thereupon; (b) a dispenser, being at a first potential relative to the precipitation electrode so as to generate an electric field between the precipitation electrode and the dispenser, the dispenser being for: (i) charging the liquefied polymer thereby providing a charged liquefied polymer; and (ii) dispensing the charged liquefied polymer in a direction of the precipitation electrode; and (c) a subsidiary electrode being at a second potential relative to the precipitation electrode, the subsidiary electrode being for modifying the electric field between the precipitation electrode and the dispenser.
According to another aspect of the present invention there is provided a method for forming a liquefied polymer into a non-woven polymer fiber shells, the method comprising: (a) charging the liquefied polymer thereby producing a charged liquefied polymer; (b) subjecting the charged liquefied polymer to a first electric field; (c) dispensing the charged liquefied polymer within the first electric field in a direction of a precipitation electrode, the precipitation electrode being designed and configured for generating the polymer fiber shell; (d) providing a second electric field being for modifying the first electric field; and (e) using the precipitation electrode to collect the charged liquefied polymer thereupon, thereby forming the non-woven polymer fiber shell.
According to further features in preferred embodiments of the invention described below, the first electric field is defined between the precipitation electrode and a dispensing electrode being at a first potential relative to the precipitation electrode.
According to still further features in the described preferred embodiments step (c) is effected by dispensing the charged liquefied polymer from the dispensing electrode.
According to still further features in the described preferred embodiments the second electric field is defined by a subsidiary electrode being at a second potential relative to the precipitation electrode.
According to still further features in the described preferred embodiments the subsidiary electrode serves for reducing non-uniformities in the first electric field
According to still further features in the described preferred embodiments the subsidiary electrode serves for controlling fiber orientation of the polymer fiber shell generated upon the precipitation electrode. According to still further features in the described preferred embodiments the subsidiary electrode serves to minimize a volume charge generated between the dispenser and the precipitation electrode.
According to still further features in the described preferred embodiments the method further comprising moving the subsidiary electrode along the precipitation electrode during step (e).
According to still further features in the described preferred embodiments the method further comprising moving the dispensing electrode along the precipitation electrode during step (c). According to still further features in the described preferred embodiments the method further comprising synchronizing the motion of the dispensing electrode and the subsidiary electrode along the precipitation electrode.
According to still further features in the described preferred embodiments the dispenser comprises a mechanism for forming a jet of the charged liquefied polymer.
According to still further features in the described preferred embodiments the apparatus further comprising a bath for holding the liquefied polymer. According to still further features in the described preferred embodiments the mechanism for forming a jet of the charged liquefied polymer includes a dispensing electrode.
According to still further features in the described preferred embodiments the dispenser is operative to move along a length of the precipitation electrode.
According to still further features in the described preferred embodiments the precipitation electrode includes at least one rotating mandrel.
According to still further features in the described preferred embodiments the rotating mandrel is a cylindrical mandrel. According to still further features in the described preferred embodiments the rotating mandrel is an intricate-profile mandrel.
According to still further features in the described preferred embodiments the intricate-profile mandrel includes sharp structural elements.
According to still further features in the described preferred embodiments the cylindrical mandrel is of a diameter selected from a range of 0.1 to 20 millimeters.
According to still further features in the described preferred embodiments the precipitation electrode includes at least one structural element selected from the group consisting of a protrusion, an orifice, a groove, and a grind.
According to still further features in the described preferred embodiments the subsidiary electrode is of a shape selected from the group consisting of a plane, a cylinder, a torus and a wire.
According to still further features in the described preferred embodiments the subsidiary electrode is operative to move along a length of the precipitation electrode.
According to still further features in the described preferred embodiments the subsidiary electrode is tilted at angle with respect to a longitudinal axis of the precipitation electrode, the angle is ranging between 45 and 90 degrees.
According to still further features in the described preferred embodiments the subsidiary electrode is positioned at a distance of 5 - 70 millimeters from the precipitation electrode.
According to still further features in the described preferred embodiments the subsidiary electrode is positioned at a distance δ from the precipitation electrode, δ being equal to 12βR(l-V2/Nι), where β is a constant ranging between about 0.7 and about 0.9, R is the curvature-radius of the polymer fiber shell formed on the precipitation electrode, Vi is the first potential and V2 is the second potential.
According to yet another aspect of the present invention there is provided an apparatus for manufacturing a polymer fiber shells from liquefied polymer, the apparatus comprising: (a) a dispenser, for: (i) charging the liquefied polymer thereby providing a charged liquefied polymer; and (ii) dispensing the charged liquefied polymer; and (b) a precipitation electrode being at a potential relative to the dispenser thereby generating an electric field between the precipitation electrode and the dispenser, the precipitation electrode being for collecting the charged liquefied polymer drawn by the electric field, to thereby form the polymer fiber shell thereupon, wherein the precipitation electrode is designed so as to reduce non-uniformities in the electric field.
According to still further features in the described preferred embodiments the precipitation electrode is formed from a combination of electroconductive and non-electroconductive materials.
According to still further features in the described preferred embodiments a surface of the precipitation electrode is formed by a predetermined pattern of the electroconductive and non-electroconductive materials.
According to still further features in the described preferred embodiments the precipitation electrode is formed from at least two layers.
According to still further features in the described preferred embodiments the at least two layers include an electroconductive layer and a partial electroconductive layer.
According to still further features in the described preferred embodiments the partial electroconductive layer is partial electroconductive layer is formed from a combination of an electroconductive material and at least one dielectric material. According to still further features in the described preferred embodiments the dielectric material is selected from a group consisting of polyamide and polyacrylonitrile and polytetrafluoroethylene.
According to still further features in the described preferred embodiments the dielectric material is Titanium Nitride.
According to still further features in the described preferred embodiments the partial electroconductive layer, is selected of a thickness ranging between 0.1 to 90 microns.
The present invention successfully addresses the shortcomings of the presently known configurations by providing an electrospinning apparatus and method capable of fabricating a non-woven polymer fiber shell which can be used in vascular grafts.
BRIEF DESCRIPTION OF THE DRAWINGS The invention is herein described, by way of example only, with reference to the accompanying drawings. With specific reference now to the drawings in detail, it is stressed that the particulars shown are by way of example and for purposes of illustrative discussion of the preferred embodiments of the present invention only, and are presented in the cause of providing what is believed to be the most useful and readily understood description of the principles and conceptual aspects of the invention. In this regard, no attempt is made to show structural details of the invention in more detail than is necessary for a fundamental understanding of the invention, the description taken with the drawings making apparent to those skilled in the art how the several forms of the invention may be embodied in practice.
In the drawings:
FIG. 1 is a schematic illustration of a prior art electrospinning apparatus; FIG. 2 is a schematic illustration of an electrospinning apparatus which includes a subsidiary electrode according to the teachings of the present invention;
FIG. 3 is a schematic illustration of an electrospinning apparatus which includes a planar subsidiary electrode according to the teachings of the present invention;
FIG. 4 is a schematic illustration of an electrospinning apparatus which includes a cylindrical subsidiary electrode according to the teachings of the present invention; FIG. 5 is a schematic illustration of an electrospinning apparatus which includes a linear subsidiary electrode according to the teachings of the present invention;
FIG. 6 is a schematic illustration of an electrospinning apparatus which includes a composite subsidiary electrode according to the teachings of the present invention;
FIG. 7 is an electron microscope image of material spun using conventional electrospinning techniques;
FIG. 8 is an electron microscope image of material spun using an apparatus which incorporates a flat subsidiary electrode, positioned 20 millimeters from the mandrel, according to the teachings of the present invention;
FIG. 9 is an electron microscope image of material spun using an apparatus which incorporates a flat subsidiary electrode, positioned 9 millimeters from the mandrel, according to the teachings of the present invention; and
FIG. 10 is an electron microscope image of polar-oriented material spun using an apparatus which incorporates a linear subsidiary electrode according to the teachings of the present invention. DESCRIPTION OF THE PREFERRED EMBODIMENTS
The present invention is of a method and an apparatus for manufacturing a polymer fiber shell using electrospinning. Specifically, the present invention can be used to manufacture intricate-profile products and vascular grafts of small to large diameter via electrospinning.
For purposes of better understanding the present invention, as illustrated in Figures 2-10 of the drawings, reference is first made to the construction and operation of a conventional (i.e., prior art) electrospinning apparatus as illustrated in Figure 1. Figure 1 illustrates an apparatus for manufacturing a tubular structure using a conventional electrospinning apparatus, which is referred to herein as apparatus 10.
Apparatus 10 includes a dispenser 12 which can be, for example, a bath provided with capillary apertures 14. Dispenser 12 serves for storing the polymer to be spun in a liquid form. Dispenser 12 is positioned at a predetermined distance from a precipitation electrode 16.
Precipitation electrode 16 serves for generating the tubular structure thereupon. Precipitation electrode 16 is typically manufactured in the form of a mandrel or any other cylindrical structure. Precipitation electrode 16 is rotated by a mechanism such that a tubular structure is formed when coated with the polymer.
Dispenser 12 is typically grounded, while precipitation electrode 16 is connected to a source of high voltage preferably of negative polarity, thus forming an electric field between dispenser 12 and precipitation electrode 16. Alternatively, precipitation electrode 16 can be grounded while dispenser 12 is connected to a source of high voltage, preferably with positive polarity.
To generate a tubular structure, a liquefied polymer (e.g., melted polymer or dissolved polymer) is extruded, for example under the action of hydrostatic pressure, through capillary apertures 14 of dispenser 12. As soon as meniscus forms from the extruded liquefied polymer, a process of solvent evaporation or cooling starts which is accompanied by the creation of capsules with a semi-rigid envelope or crust. An electric field, occasionally accompanied a by unipolar corona discharge in the area of dispenser 12, is generated by the potential difference between dispenser 12 and precipitation electrode 16. Because the liquefied polymer possesses a certain degree of electrical conductivity, the above-described capsules become charged. Electric forces of repulsion within the capsules lead to a drastic increase in hydrostatic pressure. The semi-rigid envelopes are stretched, and a number of point micro-ruptures are formed on the surface of each envelope leading to spraying of ultra-thin jets of liquefied polymer from dispenser 12.
The charges tend to distribute along the jets, thus preventing existence of any non-zero component of electric field inside the jet. Thus, a conduction current flows along the jets, which results in the accumulation of (different sign) free charges on the liquefied polymer surface.
Under the effect of a Coulomb force, the jets depart from the dispenser 12 and travel towards the opposite polarity electrode, i.e., precipitation electrode 16. Moving with high velocity in the inter-electrode space, the jet cools or solvent therein evaporates, thus forming fibers which are collected on the surface of precipitation electrode 16. Since electrode 16 is rotating the charged fibers form a tubular shape.
When using mandrels being at least partially with small radius of curvature, the orientation of the electric field maximal strength vector is such that precipitation electrode 16 is coated coaxially by the fibers. Thus, small diameter products, have limited radial strength when manufactured via existing electrospinning methods, as described above.
When using mandrels with sharp edges and/or variously shaped and sized recesses, the electric field magnitude in the vicinity of precipitation electrode 16 may exceed the air electric strength (about 30 kV/cm), and a corona discharge may develop in the area of precipitation electrode 16. The effect of corona discharge decreases the coating efficiency of the process as described hereinbelow, and may even resultant in a total inability of fibers to be collected upon precipitation electrode 16. Corona discharge initiation is accompanied by the generation of a considerable amount of air ions having opposite charge sign with respect to the charged fibers. Since an electric force is directed with respect to the polarity of charges on which it acts, theses ions start to move at the opposite direction to fibers motion i.e., from precipitation electrode 16 towards dispenser 12. Consequently, a portion of these ions generate a volume charge (ion cloud), non-uniformly distributed in the inter-electrode space, thereby causing electric field lines to partially close on the volume charge rather than on precipitation electrode 16. Moreover, the existence of an opposite volume charge in the inter-electrode space, decreases the electric force on the fibers, thus resulting in a large amount of fibers accumulating in the inter-electrode space and gradually settling under gravity force. It will be appreciated that such an effect leads to a low-efficiency process of fiber coating.
Using an infinite-length/radius cylinder as a precipitation electrode 16 diminishes the effect described above. However, this effect is severe and limiting when small radii or complicated mandrels are employed for fabricating small radius or intricate-profile structures.
Before explaining at least one embodiment of the invention in detail, it is to be understood that the invention is not limited in its application to the details of construction and the arrangement of the components set forth in the following description or illustrated in the drawings. The invention is capable of other embodiments or of being practiced or carried out in various ways. Also, it is to be understood that the phraseology and terminology employed herein is for the purpose of description and should not be regarded as limiting. While reducing the present invention to practice, it was uncovered that the use of a third electrode within an electrospinning apparatus enables to control the electric field generated between the dispenser and precipitation electrode. Specifically, a third electrode may either substantially decreases non-uniformities in the electric field or provides for controlled fiber orientation upon deposition.
Thus, according to the present invention there is provided an apparatus for manufacturing a polymer fiber shell from a liquefied polymer, which apparatus is referred to herein as apparatus 20. As shown in Figure 2, apparatus 20 includes a precipitation electrode
22 which serves for generating the polymer fiber shell thereupon.
Precipitation electrode 22 can be, for example, a mandrel of uniform or varying radius, which may include some structural elements such as, but not limited to, protrusions, orifices and grooves. The surface of precipitation electrode 22 may also contain grinds. The diameter of the mandrel may vary from about 0.1 millimeter up to about 20 millimeters depending on the diameter of the polymer fiber shell to be spun thereupon.
Apparatus 20 further includes a dispenser 24, which is at a first potential relative to precipitation electrode 22. Such a potential can be generated by grounding dispenser 24, and connecting a source of high voltage with negative polarity to precipitation electrode 22.
Alternatively, precipitation electrode 22 can be grounded while dispenser 24 is connected to a source of high voltage with positive polarity.
In any case, an absolute value for the potential difference between dispenser 24 and precipitation electrode 22 may range between about 10 kV and about 100 kV.
The potential difference between dispenser 24 and precipitation electrode 22 ensures that an electric field is maintained therebetween, which electric field is important for the electrospinning process as described hereinabove. Dispenser 24 serves for charging the liquefied polymer, thereby providing a charged liquefied polymer and dispensing the charged liquefied polymer in a direction of precipitation electrode 22. Dispenser 24 may also include a mechanism for moving it along a longitudinal axis of precipitation electrode 22, thus enabling dispensing of the charged liquefied polymer at various points along the longitudinal axis of precipitation electrode 22.
The charged liquefied polymer may be, for example polyurethane, polyester, polyolefin, polymethyl methacrylate, polyvinyl aromatic, polyvinyl ester, polyamide, polyimide, polyether, polycarbonate, polyacrilonitrile, polyvinyl pyrrolidone, polyethylene oxide, poly (L-lactic acid), poly (lactide-CD-glycoside), polycaprolactone, polyphosphate ester, poly (gly colic acid), poly (DL-lactic acid), and some copolymers. Biolmolecules such as DNA, silk, chitozan and cellulose may also be used. Improved charging of the polymer may also be required. Improved charging is effected according to the present invention by mixing the liquefied polymer with a charge control agent (e.g., a dipolar additive) to form, for example, a polymer-dipolar additive complex which apparently better interacts with ionized air molecules formed under the influence of the electric field. It is assumed, in a non-limiting fashion, that the extra-charge attributed to the newly formed fibers is responsible for their more homogenous precipitation on the precipitation electrode, wherein a fiber is better attracted to a local maximum, which is a local position most under represented by older precipitated fibers, which keep their charge for 5-10 minutes. The charge control agent is typically added in the grams equivalent per liter range, say, in the range of from about 0.001 N to about 0.1 N, depending on the respective molecular weights of the polymer and the charge control agent used.
U.S. Pat. Nos. 5,726,107; 5,554,722; and 5,558,809 teach the use of charge control agents in combination with polycondensation processes in the production of electret fibers, which are fibers characterized in a permanent electric charge, using melt spinning and other processes devoid of the use of an precipitation electrode. A charge control agent is added in such a way that it is incorporated into the melted or partially melted fibers and remains incorporated therein to provide the fibers with electrostatic charge which is not dissipating for prolonged time periods, say months.
In a preferred embodiment of the present invention, the charge control agent transiently binds to the outer surface of the fibers and therefore the charge dissipates shortly thereafter (within minutes). This is because polycondensation is not exercised at all such the chemical intereaction between the agent and the polymer is absent, and further due to the low concentration of charge control agent employed. The resulting shell is therefore substantially charge free.
Suitable charge control agents include, but are not limited to, mono- and poly-cyclic radicals that can bind to the polymer molecule via, for example, -C=C-, =C-SH- or -CO-NH- groups, including biscationic amides, phenol and uryl sulfide derivatives, metal complex compounds, triphenylmethanes, dimethylmidazole and ethoxytrimethylsians.
Typically, the charged liquefied polymer is dispensed as a liquid jet, moving at high velocity under electrical forces caused by the electric field. Thus, dispenser 24 typically includes a bath for holding the liquefied polymer and a mechanism for forming a jet, which mechanism may be, for example, a dispensing electrode.
Apparatus 20 further includes at least one subsidiary electrode 26 which is at a second potential relative to precipitation electrode 22. Subsidiary electrode 26 serves for controlling the direction and magnitude of the electric field between precipitation electrode 22 and dispenser 24 and as such, subsidiary electrode 26 can be used to control the orientation of polymer fibers deposited on precipitation electrode 22. In some embodiments, subsidiary electrode 26 serves as a supplementary screening electrode. Broadly stated, use of screening results in decreasing the coating precipitation factor, which is particularly important upon mandrels having at least a section of small radii of curvature.
The size, shape, position and number of subsidiary electrode 26 is selected so as to maximize the coating precipitation factor, while minimizing the effect of corona discharge in the area of precipitation electrode 22 and/or so as to provide for controlled fiber orientation upon deposition.
According to one preferred embodiment of the present invention, subsidiary electrode 26 is positioned 5-70 mm away from precipitation electrode 22.
Preferably, such a distance is selected according to the following:
Figure imgf000017_0001
where β is a dimensionless constant named a fiber-charge accounting factor, which ranges between about 0.7 and about 0.9, R is the curvature-radius of precipitation electrode 22, V! is the potential difference between dispenser 24 and precipitation electrode 22 and V2 is the potential difference between subsidiary electrode 26 and precipitation electrode 22. Subsidiary electrode 26 may include a mechanism for moving it along a longitudinal axis of precipitation electrode 22. Such a mechanism may be in use when enhanced control over fiber orientation is required.
It will be appreciated that in an apparatus in which both dispenser 24 and subsidiary electrode 26 are capable of such longitudinal motion, such motion may be either independent or synchronized.
Subsidiary electrode 26 may also be tilted through an angle of 45-90 degrees with respect to the longitudinal axis of precipitation electrode 22. Such tilting may be used to provide for controlled fiber orientation upon deposition, hence to control the radial strength of the manufactured shell; specifically, large angles result in higher radial strength. In addition to positioning, the shape and size of electrode 26 may also determine the quality of the shell formed by apparatus 20. Thus, electrode 26 may be fabricated in a variety of shapes each serving a specific purpose. Electrode shapes which can be used with apparatus 20 of the present invention include, but are not limited to, a plane, a cylinder, a torus a rod, a knife, an arc or a ring.
An apparatus 20 which includes a subsidiary electrode 26 of a cylindrical (Figure 4) or a flat shape (Figure 3) enables manufacturing intricate-profile products being at least partially with small radius of curvature, which radius may range between 0.025 millimeters and 5 millimeters. As can be seen in Figures 8-9 (further described in the Examples section), the coating of such structures is characterized by random-oriented (Figure 8) or even polar-oriented (Figure 9) fibers, as opposed to an axial coating which is typical for small curvature products manufactured via existing electrospinning methods as demonstrated in Figure 7 (further described in the Examples section).
Preferably, when a surface of large curvature is used as subsidiary electrode 26, as is the case above, the distance between subsidiary electrode
26 and precipitation electrode 22 can be determined as δ/x where x is a factor ranging between 1.8 and 2, and where δ is as defined by Equation 1 above.
Thus, positioning and/or shape of electrode 26 determines fiber orientation in the polymer fiber shell formed.
The ability to control fiber orientation is important when fabricating vascular grafts in which a high radial strength and elasticity is important. It will be appreciated that a polar oriented structure can generally be obtained also by wet spinning methods, however in wet spinning methods the fibers are thicker than those used by electrospinning by at least an order of magnitude. Control over fiber orientation is also advantageous when fabricating composite polymer fiber shells which are manufactured by sequential deposition of several different fiber materials.
Reference is now made to Figure 5, which illustrates an apparatus 20 which utilizes a linear (e.g., a rod, a knife, an arc or a ring) subsidiary electrode 26.
The effect of subsidiary electrode 26 of linear shape is based on the distortion it introduces to the electric field in an area adjacent to precipitation electrode 22. For maximum effect the diameter of subsidiary electrode 26 must be considerably smaller than that of precipitation electrode 22, yet large enough to avoid generation of a significant corona discharge. Fiber coating generated by apparatus 20 utilizing a linear subsidiary electrode 26 is illustrated by Figure 10 which is further described in the Examples section hereinunder. Thus, the present invention provides an electrospinning apparatus in which the electric field is under substantial control, thereby providing either random or predetermined fibers orientation.
Although the use of at least one subsidiary electrode is presently preferred, field non-uniformities can also be at least partially overcome by providing a composite precipitation electrode.
As illustrated in Figure 6, precipitation electrode 34 of apparatus 30 having a dispenser 32 can be designed and configured so as to reduce non-uniformities in the electric field.
To overcome field non-uniformities, precipitation electrode 34 is fabricated from at least two layers of materials, an inner layer 36 made of electroconductive material and an outer layer 38 made of a material having high dielectric properties. Such a fabrication design results in a considerable increase of corona discharge threshold thus considerably reducing corona discharge from precipitation electrode 34. Materials suitable for use with outer layer 38 of precipitation electrode 34, can be ceramic materials e.g., Titanium Nitride, Aluminum
Oxide and the like, or polymer materials e.g., polyamide, polyacrylonitrile, polytetrafluoroethylene and the like. The thickness of outer layer 38 depends on the dielectric properties of the material from which it is made and can vary from less than one micron, in the case of, for example, a
Titanium Nitride layer, or tens of microns, in the case of, for example, polytetrafluoroethylene, polyamide or polyacrylonitrile layer. In addition to diminishing corona discharge this precipitation electrode configuration enables easier separation of formed structures therefrom. Thus, according to this configuration outer layer 38 of precipitation electrode 34 can also be configured for facilitating the removal of the final product from the mandrel.
Additional objects, advantages, and novel features of the present invention will become apparent to one ordinarily skilled in the art upon examination of the following"' examples, which are not intended to be limiting. Additionally, each of the various embodiments and aspects of the present invention as delineated hereinabove and as claimed in the claims section below finds experimental support in the following examples.
EXAMPLES
Reference is now made to the following examples, which together with the above descriptions, illustrate the invention in a non limiting fashion.
Electrospinning Material
A polycarbonate resin grade Caliper 2071 was purchased from Daw Chemical Co. This Polymer is characterized as having good fiber forming abilities and is convenient for electrospinning. Chloroform was used as solvent in all of the examples described hereinbelow.
EXAMPLE 1 Axial Covering Using Conventional Electrospinning Method
Reference is now made to Figure 7, which is an example of non-randomized covering of thin mandrels via conventional electrospinning. A 3-mm cylindrical mandrel was covered by polycarbonate fiber using prior art electrospinning approaches. Figure 7 is an electron microscope image of the final product, in which axial fiber orientation is well evident. Due to non-uniformities in the electric field, the fibers, while still in motion in the inter-electrode space, are oriented in conformity with the field configuration, and the obtained tubular structure exhibits axial orientation of fibers, and as such is characterized by axial, as opposed to radial strength.
EXAMPLE 2 Random Covering Using Flat Subsidiary Electrode
An apparatus constructed and operative in accordance with the teachings of the present invention incorporating a flat subsidiary electrode positioned 20 millimeters from the mandrel and having the same potential as the mandrel was used to spin a polycarbonate tubular structure of a 3 mm radius. As is evident from Figure 8, the presence of a subsidiary electrode randomizes fibers orientation.
EXAMPLE 3 Polar-Oriented Covering Using Flat Subsidiary electrode An apparatus constructed and operative in accordance with the teachings of the present invention incorporating a flat subsidiary electrode positioned 9 millimeters from the mandrel and being at a potential difference of 5 kV from the mandrel was used to spin a polycarbonate tubular structure of a 3 mm radius.
As illustrated by Figure 9, reduction of equalizing electrode-mandrel distance results in polar-oriented covering. Thus, by keeping subsidiary electrode and mandrel within a relatively small distance, while providing a non-zero potential difference therebetween, leads to slow or no fiber charge dissipation and, as a result, the inter-electrode space becomes populated with fiber which are held statically in a stretched position, oriented perpendicular to mandrel symmetry axis. Once stretched, the fibers are gradually coiled around the rotating mandrel, generating a polar-oriented structure.
EXAMPLE 4 Predefined Oriented Covering Using Linear Subsidiary electrode Figure 10 illustrates result obtained from an apparatus configuration which may be employed in order to obtain a predefined oriented structural fiber covering.
An apparatus which includes an elliptical subsidiary electrode and a dispenser both moving along the longitudinal axis of the mandrel in a reciprocating synchronous movement was used to coat a 3-mm cylindrical mandrel with polycarbonate fiber. The subsidiary electrode had a large diameter of 120 mm, a small diameter of 117.6 mm and a thickness of 1.2 mm. The subsidiary electrode was positioned 15 mm from the mandrel, at an 80 ° tilt with respect to the mandrel symmetry axis. It is appreciated that certain features of the invention, which are, for clarity, described in the context of separate embodiments, may also be provided in combination in a single embodiment. Conversely, various features of the invention, which are, for brevity, described in the context of a single embodiment, may also be provided separately or in any suitable subcombination. Although the invention has been described in conjunction with specific embodiments thereof, it is evident that many alternatives, modifications and variations will be apparent to those skilled in the art. Accordingly, it is intended to embrace all such alternatives, modifications and variations that fall within the spirit and broad scope of the appended claims. All publications, patents and patent applications mentioned in this specification are herein incorporated in their entirety by reference into the specification, to the same extent as if each individual publication, patent or patent application was specifically and individually indicated to be incorporated herein by reference. In addition, citation or identification of any reference in this application shall not be construed as an admission that such reference is available as prior art to the present invention.

Claims

WHAT IS CLAIMED IS:
1. An apparatus for manufacturing polymer fiber shell from liquefied polymer, the apparatus comprising:
(a) a precipitation electrode being for generating the polymer fiber shell thereupon;
(b) a dispenser, being at a first potential relative to said precipitation electrode so as to generate an electric field between said precipitation electrode and said dispenser, said dispenser being for:
(i) charging the liquefied polymer thereby providing a charged liquefied polymer; and (ii) dispensing said charged liquefied polymer in a direction of said precipitation electrode; and
(c) a subsidiary electrode being at a second potential relative to said precipitation electrode, said subsidiary electrode being for modifying said electric field between said precipitation electrode and said dispenser.
2. The apparatus of claim 1, wherein said subsidiary electrode serves for reducing non-uniformities in said electric field between said precipitation electrode and said dispenser.
3. The apparatus of claim 1, wherein said subsidiary electrode serves for controlling fiber orientation of said polymer fiber shell generated upon said precipitation electrode.
4. The apparatus according to claim 1, wherein said dispenser comprises a mechanism for forming a jet of said charged liquefied polymer.
5. The apparatus according to claim 1, further comprising a bath for holding the liquefied polymer.
6. The apparatus according to claim 4, wherein said mechanism for foπning a jet of said charged liquefied polymer includes a dispensing electrode.
7. The apparatus according to claim 1, wherein said dispenser is operative to move along a longitudinal axis of said precipitation electrode.
8. The apparatus according to claim 1, wherein said precipitation electrode includes at least one rotating mandrel.
9. The apparatus according to claim 8, wherein said rotating mandrel is a cylindrical mandrel.
10. The apparatus according to claim 9, wherein said cylindrical mandrel is of a diameter selected from a range of 0.1 to 20 millimeters.
11. The apparatus according to claim 8, wherein said rotating mandrel is an intricate-profile mandrel.
12. The apparatus according to claim 11, wherein said intricate-profile mandrel includes sharp structural elements.
13. The apparatus according to claim 1 , wherein said precipitation electrode includes at least one structural element selected from the group consisting of a protrusion, an orifice, a groove, and a grind.
14. The apparatus according to claim 1, wherein said subsidiary electrode is of a shape selected from the group consisting of a plane, a cylinder, a torus and a wire.
15. The apparatus according to claim 1, wherein said subsidiary electrode is operative to move along a longitudinal axis of said precipitation electrode.
16. The apparatus according to claim 1, wherein said subsidiary electrode is tilted at angle with respect to a longitudinal axis of said precipitation electrode, said angle is ranging between 45 and 90 degrees.
17. The apparatus according to claim 1, wherein said subsidiary electrode is positioned at a distance of 5 - 70 millimeters from said precipitation electrode.
18. The apparatus according to claim 1, wherein said subsidiary electrode is positioned at a distance δ from said precipitation electrode, δ being equal to 12βR(l-V2/V , where β is a constant ranging between about 0.7 and about 0.9, R is a curvature-radius of the polymer fiber shell formed on said precipitation electrode, Vi is said first potential and V2 is said second potential.
19. A method for forming a liquefied polymer into a non- woven polymer fiber shell, the method comprising:
(a) charging the liquefied polymer thereby producing a charged liquefied polymer;
(b) subjecting said charged liquefied polymer to a first electric field;
(c) dispensing said charged liquefied polymer within said first electric field in a direction of a precipitation electrode, said precipitation electrode being designed and configured for generating the polymer fiber shell thereupon;
(d) providing a second electric field being for modifying said first electric field; and
(e) using said precipitation electrode to collect said charged liquefied polymer thereupon, thereby forming the non-woven polymer fiber shells.
20. The method according to claim 19, wherein said first electric field is defined between said precipitation electrode and a dispensing electrode being at a first potential relative to said precipitation electrode.
21. The method according to claim 20, wherein step (c) is effected by dispensing said charged liquefied polymer from said dispensing electrode.
22. The method according to claim 19, further comprising moving said dispensing electrode along a longitudinal axis of said precipitation electrode during step (c).
23. The method according to claim 19, wherein said precipitation electrode includes at least one rotating mandrel.
24. The method according to claim 23, wherein said rotating mandrel is a cylindrical mandrel.
25. The method according to claim 24, wherein said cylindrical mandrel is of a diameter selected from a range of 0.1 to 20 millimeters.
26. The method according to claim 23, wherein said rotating mandrel is an intricate-profile mandrel.
27. The method according to claim 26, wherein said intricate-profile mandrel includes sharp structural elements.
28. The method according to claim 25, wherein said precipitation electrode includes at least one structural element selected from the group consisting of a protrusion, an orifice, a groove, and a grind.
29. The method according to claim 20, wherein said second electric field is defined by a subsidiary electrode being at a second potential relative to said precipitation electrode.
30. The method according to claim 29, wherein said subsidiary electrode serves for reducing non-uniformities in said first electric field.
31. The method according to claim 19, wherein said subsidiary electrode serves for controlling fiber orientation of said polymer fiber shell generated upon said precipitation electrode.
32. The method according to claim 29, wherein said subsidiary electrode is of a shape selected from the group consisting of a plane, a cylinder, a torus and a wire.
33. The method according to claim 29, further comprising moving said subsidiary electrode along said precipitation electrode during step (e).
34. The method according to claim 29, further comprising tilting said subsidiary electrode at angle with respect to a longitudinal axis of said precipitation electrode, said angle ranging between 45 and 90 degrees.
35. The method according to claim 29, wherein said subsidiary electrode is positioned at a distance of 5 - 50 millimeters from said precipitation electrode.
36. The method according to claim 29, wherein said subsidiary electrode is positioned at a distance δ from said precipitation electrode, δ being equal to 12βR(l-V2/V1), where β is a constant ranging between about 0.7 and about 0.9, R is a curvature-radius of the polymer fiber shell foπned on said precipitation electrode, Vi is said first potential and V2 is said second potential.
37. An apparatus for manufacturing a polymer fiber shell from liquefied polymer, the apparatus comprising:
(a) a dispenser, for:
(i) charging the liquefied polymer thereby providing a charged liquefied polymer; and (ii) dispensing said charged liquefied polymer; and
(b) a precipitation electrode being at a potential relative to said dispenser thereby generating an electric field between said precipitation electrode and said dispenser, said precipitation electrode being for collecting said charged liquefied polymer drawn by said electric field, to thereby form the polymer fiber shell thereupon, wherein said precipitation electrode is designed so as to reduce non-uniformities in said electric field.
38. The apparatus according to claim 37, wherein said dispenser comprises a mechanism for forming a jet of said charged liquefied polymer.
39. The apparatus according to claim 37, further comprising a bath for holding the liquefied polymer.
40. The apparatus according to claim 38, wherein said mechanism for forming a jet of said charged liquefied polymer includes a dispensing electrode.
41. The apparatus according to claim 37, wherein said precipitation electrode is formed from a combination of electroconductive and non-electroconductive materials.
42. The apparatus according to claim 41, wherein a surface of said precipitation electrode is formed from a predetermined pattern of said electroconductive and non-electroconductive materials.
43. The apparatus according to claim 37, wherein said precipitation electrode is formed from at least two layers.
44. The apparatus according to claim 43, wherein said at least two layers include an electroconductive layer and a partial electroconductive layer.
45. The apparatus according to claim 44, wherein said partial electroconductive layer is formed from a combination of an electroconductive material and at least one dielectric material.
46. The apparatus according to claim 45, wherein said dielectric material is selected from a group consisting of polyamide, polytetrafluoroethylene and polyacrylonitrile.
47. The apparatus according to claim 45, wherein said dielectric material is Titanium Nitride.
48. The apparatus according to claim 44, wherein said partially electroconductive layer, is of a thickness selected from a range of 0.1 to 90 microns.
49. The apparatus according to claim 37, wherein said precipitation electrode is of a diameter selected from a range of 0.1 to 20 millimeters.
50. The apparatus according to claim 37, wherein said precipitation electrode includes at least one rotating mandrel.
51. The apparatus according to claim 50, wherein said rotating mandrel is a cylindrical mandrel.
52. A tubular structure manufactured by the apparatus of claim 1.
53. A tubular structure manufactured by the method of claim 29.
54. A tubular structure manufactured by the apparatus of claim
37.
55. The apparatus of claim 1, wherein said subsidiary electrode serves to minimize a volume charge generated between said dispenser and said precipitation electrode.
56. The method according to claim 29, wherein said subsidiary electrode serves to minimize a volume charge generated between said precipitation electrode and said dispensing electrode.
57. The apparatus according to claim 1, wherein said dispenser and said subsidiary electrode are operative to move synchromcally along a longitudinal axis of said precipitation electrode.
58. The method according to claim 29, further comprising synchromcally moving both said dispensing electrode and said subsidiary electrode along said precipitation electrode.
PCT/IL2001/001168 2000-12-19 2001-12-17 Method and apparatus for manufacturing polymer fiber shells via electrospinning WO2002049678A2 (en)

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MXPA03005551A MXPA03005551A (en) 2000-12-19 2001-12-17 Method and apparatus for manufacturing polymer fiber shells via electrospinning.
US10/433,621 US7112293B2 (en) 2000-12-19 2001-12-17 Method and apparatus for manufacturing polymer fiber shells via electrospinning
JP2002551015A JP2005507464A (en) 2000-12-19 2001-12-17 Method and apparatus for producing polymer fiber shells by electrospinning
IL15651301A IL156513A0 (en) 2000-12-19 2001-12-17 Method and apparatus for manufacturing polymer fiber shells via electrospinning
EP01271232A EP1355677B1 (en) 2000-12-19 2001-12-17 Method and apparatus for manufacturing polymer fiber shells via electrospinning
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AT01271232T ATE460903T1 (en) 2000-12-19 2001-12-17 METHOD AND APPARATUS FOR PRODUCING POLYMER FIBER COVERS BY ELECTROSPINNING
IL156513A IL156513A (en) 2000-12-19 2003-06-18 Method and apparatus for manufacturing polymer fiber shells via electrospinning
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Cited By (18)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2004256973A (en) * 2003-02-27 2004-09-16 Japan Vilene Co Ltd Method for electrospinning and device for electrospinning
JP2004256974A (en) * 2003-02-27 2004-09-16 Japan Vilene Co Ltd Method for electrospinning and device for electrospinning
WO2005042813A1 (en) * 2003-10-30 2005-05-12 Clean Air Technology Corp. Electrostatic spinning equipment and method of preparing nano fiber using the same
WO2005064048A1 (en) * 2003-12-30 2005-07-14 Raisio Chemicals Korea Inc. A method manufacturing nano-fibers with excellent fiber formation
WO2005095684A1 (en) * 2004-03-25 2005-10-13 Massachusetts Institute Of Technology Production of submicron diameter fibers by two-fluid electrospinning process
US7134857B2 (en) 2004-04-08 2006-11-14 Research Triangle Institute Electrospinning of fibers using a rotatable spray head
US7297305B2 (en) 2004-04-08 2007-11-20 Research Triangle Institute Electrospinning in a controlled gaseous environment
US7592277B2 (en) 2005-05-17 2009-09-22 Research Triangle Institute Nanofiber mats and production methods thereof
US7762801B2 (en) 2004-04-08 2010-07-27 Research Triangle Institute Electrospray/electrospinning apparatus and method
EP2314739A1 (en) * 2009-10-22 2011-04-27 Gyeong-Man Kim Anti-migration casing for transponders
US8425810B2 (en) 2009-02-05 2013-04-23 Panasonic Corporation Nanofiber production device and nanofiber production method
WO2016199139A1 (en) 2015-06-08 2016-12-15 Corneat Vision Ltd Keratoprosthesis and uses thereof
WO2018081554A1 (en) * 2016-10-27 2018-05-03 North Carolina State University 3d printing of fibrous structures
US10307292B2 (en) 2011-07-18 2019-06-04 Mor Research Applications Ltd Device for adjusting the intraocular pressure
WO2019234741A1 (en) 2018-06-05 2019-12-12 Corneat Vision Ltd. A synthetic ophthalmic graft patch
WO2020217244A1 (en) 2019-04-25 2020-10-29 Corneat Vision Ltd. Keratoprosthesis devices and kits and surgical methods of their use
WO2021028912A1 (en) 2019-08-12 2021-02-18 Corneat Vision Ltd. Gingival graft
WO2023161945A1 (en) 2022-02-27 2023-08-31 Corneat Vision Ltd. Implantable sensor

Families Citing this family (267)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070219642A1 (en) * 1998-12-03 2007-09-20 Jacob Richter Hybrid stent having a fiber or wire backbone
US20040267349A1 (en) * 2003-06-27 2004-12-30 Kobi Richter Amorphous metal alloy medical devices
US8382821B2 (en) 1998-12-03 2013-02-26 Medinol Ltd. Helical hybrid stent
US7615373B2 (en) * 1999-02-25 2009-11-10 Virginia Commonwealth University Intellectual Property Foundation Electroprocessed collagen and tissue engineering
US20020081732A1 (en) * 2000-10-18 2002-06-27 Bowlin Gary L. Electroprocessing in drug delivery and cell encapsulation
EP1315756A2 (en) * 2000-09-01 2003-06-04 Virginia Commonwealth University Intellectual Property Foundation Electroprocessed fibrin-based matrices and tissues
US7270693B2 (en) * 2000-09-05 2007-09-18 Donaldson Company, Inc. Polymer, polymer microfiber, polymer nanofiber and applications including filter structures
US6743273B2 (en) 2000-09-05 2004-06-01 Donaldson Company, Inc. Polymer, polymer microfiber, polymer nanofiber and applications including filter structures
US20020084178A1 (en) * 2000-12-19 2002-07-04 Nicast Corporation Ltd. Method and apparatus for manufacturing polymer fiber shells via electrospinning
US20070031607A1 (en) * 2000-12-19 2007-02-08 Alexander Dubson Method and apparatus for coating medical implants
RU2300543C2 (en) * 2001-05-31 2007-06-10 Дональдсон Компани, Инк. Fine fiber compositions, methods for preparation thereof, and a method of manufacturing fine-fiber material
WO2003087443A1 (en) * 2002-04-11 2003-10-23 Secant Medical, Inc. Covering process using electrospinning of very small fibers
JP5445649B2 (en) * 2002-08-23 2014-03-19 独立行政法人国立循環器病研究センター Stent
GB0223870D0 (en) * 2002-10-14 2002-11-20 Cathnet Science Holding As Stent assembly
US6949916B2 (en) * 2002-11-12 2005-09-27 Power-One Limited System and method for controlling a point-of-load regulator
US20040098023A1 (en) * 2002-11-15 2004-05-20 Scimed Life Systems, Inc. Embolic device made of nanofibers
JP4047739B2 (en) * 2003-02-04 2008-02-13 日本バイリーン株式会社 Electrostatic spinning method and electrostatic spinning apparatus
US7658747B2 (en) 2003-03-12 2010-02-09 Nmt Medical, Inc. Medical device for manipulation of a medical implant
US7452374B2 (en) * 2003-04-24 2008-11-18 Maquet Cardiovascular, Llc AV grafts with rapid post-operative self-sealing capabilities
JP4496360B2 (en) * 2003-04-24 2010-07-07 国立大学法人九州大学 Medical Polymer Nano / Microfiber
JP4971580B2 (en) * 2003-06-05 2012-07-11 テルモ株式会社 Stent and method for manufacturing stent
US9039755B2 (en) 2003-06-27 2015-05-26 Medinol Ltd. Helical hybrid stent
US9155639B2 (en) 2009-04-22 2015-10-13 Medinol Ltd. Helical hybrid stent
FR2858543B1 (en) * 2003-08-08 2006-02-03 Assist Publ Hopitaux De Paris AORTIC AND ANCILLARY RING FOR ITS INSTALLATION
CZ20032421A3 (en) * 2003-09-08 2004-11-10 Technická univerzita v Liberci Process for producing nanofibers of polymer solution by electrostatic spinning and apparatus for making the same
US20070207179A1 (en) * 2003-10-14 2007-09-06 Erik Andersen Medical Device
DE10350287A1 (en) 2003-10-24 2005-05-25 Deutsche Institute für Textil- und Faserforschung Stuttgart - Stiftung des öffentlichen Rechts Cardiovascular implant, for use as a vascular or heart valve replacement, comprises a non-resorbable polymer formed as a microfiber fleece that allows colonization by a cells
WO2005055834A1 (en) * 2003-11-20 2005-06-23 Nmt Medical, Inc. Device, with electrospun fabric, for a percutaneous transluminal procedure, and methods thereof
US20080200975A1 (en) * 2004-01-06 2008-08-21 Nicast Ltd. Vascular Prosthesis with Anastomotic Member
DK1709218T3 (en) * 2004-01-30 2010-05-03 Park Jong Cheol Electrospinning device that works from the bottom up
US20050192626A1 (en) 2004-01-30 2005-09-01 Nmt Medical, Inc. Devices, systems, and methods for closure of cardiac openings
US8057841B2 (en) 2004-02-12 2011-11-15 University Of Akron Mechanically attached medical device coatings
US20060142838A1 (en) * 2004-12-29 2006-06-29 Masoud Molaei Medical devices including metallic films and methods for loading and deploying same
US8998973B2 (en) * 2004-03-02 2015-04-07 Boston Scientific Scimed, Inc. Medical devices including metallic films
US20050197687A1 (en) * 2004-03-02 2005-09-08 Masoud Molaei Medical devices including metallic films and methods for making same
US8632580B2 (en) * 2004-12-29 2014-01-21 Boston Scientific Scimed, Inc. Flexible medical devices including metallic films
US7901447B2 (en) * 2004-12-29 2011-03-08 Boston Scientific Scimed, Inc. Medical devices including a metallic film and at least one filament
US8591568B2 (en) * 2004-03-02 2013-11-26 Boston Scientific Scimed, Inc. Medical devices including metallic films and methods for making same
US8992592B2 (en) * 2004-12-29 2015-03-31 Boston Scientific Scimed, Inc. Medical devices including metallic films
EP1725703B1 (en) * 2004-03-16 2009-06-10 University Of Delaware Active and adaptive photochromic fibers,textiles and membranes
JP4312090B2 (en) * 2004-03-18 2009-08-12 日本バイリーン株式会社 Method for manufacturing fiber assembly and apparatus for manufacturing fiber assembly by electrostatic spinning
JP2005278993A (en) * 2004-03-30 2005-10-13 Terumo Corp Stent for indwelling in living body, and production method of the same
JP2007534389A (en) * 2004-04-29 2007-11-29 キューブ・メディカル・アクティーゼルスカブ Balloon used for angiogenesis
NL1026076C2 (en) 2004-04-29 2005-11-01 Univ Eindhoven Tech Molded part manufactured by means of electro-spinning and a method for the manufacture thereof as well as the use of such a molded part.
US20060012084A1 (en) * 2004-07-13 2006-01-19 Armantrout Jack E Electroblowing web formation process
WO2006026725A2 (en) 2004-08-31 2006-03-09 C.R. Bard, Inc. Self-sealing ptfe graft with kink resistance
US9801982B2 (en) 2004-09-28 2017-10-31 Atrium Medical Corporation Implantable barrier device
WO2006036967A1 (en) 2004-09-28 2006-04-06 Atrium Medical Corporation Solubilizing a drug for use in a coating
US8962023B2 (en) 2004-09-28 2015-02-24 Atrium Medical Corporation UV cured gel and method of making
US9012506B2 (en) 2004-09-28 2015-04-21 Atrium Medical Corporation Cross-linked fatty acid-based biomaterials
US9000040B2 (en) 2004-09-28 2015-04-07 Atrium Medical Corporation Cross-linked fatty acid-based biomaterials
JP5042025B2 (en) * 2004-09-29 2012-10-03 ナショナル ユニヴァーシティー オブ シンガポール COMPOSITE, COMPOSITE MANUFACTURING METHOD, AND USE THEREOF
US7390760B1 (en) * 2004-11-02 2008-06-24 Kimberly-Clark Worldwide, Inc. Composite nanofiber materials and methods for making same
US20060094320A1 (en) * 2004-11-02 2006-05-04 Kimberly-Clark Worldwide, Inc. Gradient nanofiber materials and methods for making same
US8029563B2 (en) * 2004-11-29 2011-10-04 Gore Enterprise Holdings, Inc. Implantable devices with reduced needle puncture site leakage
US7922761B2 (en) * 2005-01-25 2011-04-12 Nicast Ltd. Artificial vascular prosthesis
US10328032B2 (en) 2005-03-04 2019-06-25 Biosurfaces, Inc. Nanofibrous materials as drug, protein, or genetic release vehicles
KR20070110024A (en) * 2005-03-10 2007-11-15 메사추세츠 인스티튜트 오브 테크놀로지 Superhydrophobic fibers and methods of preparation and use thereof
US7737131B2 (en) * 2005-03-31 2010-06-15 University Of Delaware Multifunctional and biologically active matrices from multicomponent polymeric solutions
US8415325B2 (en) * 2005-03-31 2013-04-09 University Of Delaware Cell-mediated delivery and targeted erosion of noncovalently crosslinked hydrogels
US8367639B2 (en) 2005-03-31 2013-02-05 University Of Delaware Hydrogels with covalent and noncovalent crosslinks
US7732427B2 (en) * 2005-03-31 2010-06-08 University Of Delaware Multifunctional and biologically active matrices from multicomponent polymeric solutions
EP1868660B1 (en) * 2005-04-04 2016-08-03 Technion Research & Development Foundation Limited Medical scaffold, methods of fabrication and using thereof
US7854760B2 (en) * 2005-05-16 2010-12-21 Boston Scientific Scimed, Inc. Medical devices including metallic films
JP2008540022A (en) * 2005-05-17 2008-11-20 ナイキャスト リミテッド Implantable charged medical device
US8267993B2 (en) 2005-06-09 2012-09-18 Coroneo, Inc. Expandable annuloplasty ring and associated ring holder
CA2610896C (en) * 2005-06-17 2014-07-08 C.R. Bard, Inc. Vascular graft with kink resistance after clamping
GB2427382A (en) * 2005-06-21 2006-12-27 Univ Sheffield Electrospinning of fibres
CN100531685C (en) * 2005-07-20 2009-08-26 同济大学 Tissue engineering blood vessel and method of construction in vitro
FR2898502B1 (en) * 2006-03-16 2012-06-15 Sofradim Production THREE DIMENSIONAL PROTHETIC FABRIC WITH RESORBABLE DENSE FACE
US20070036842A1 (en) * 2005-08-15 2007-02-15 Concordia Manufacturing Llc Non-woven scaffold for tissue engineering
US7465159B2 (en) * 2005-08-17 2008-12-16 E.I. Du Pont De Nemours And Company Fiber charging apparatus
US7582247B2 (en) * 2005-08-17 2009-09-01 E. I. Du Pont De Nemours And Company Electroblowing fiber spinning process
US20070048351A1 (en) * 2005-09-01 2007-03-01 Prescient Medical, Inc. Drugs coated on a device to treat vulnerable plaque
WO2007035011A1 (en) * 2005-09-26 2007-03-29 Hak-Yong Kim Conjugate electrospinning devices, conjugate nonwoven and filament comprising nanofibers prepared by using the same
US8574627B2 (en) 2006-11-06 2013-11-05 Atrium Medical Corporation Coated surgical mesh
US9427423B2 (en) 2009-03-10 2016-08-30 Atrium Medical Corporation Fatty-acid based particles
US9278161B2 (en) 2005-09-28 2016-03-08 Atrium Medical Corporation Tissue-separating fatty acid adhesion barrier
EP1933991A4 (en) 2005-10-15 2012-05-02 Atrium Medical Corp Hydrophobic cross-linked gels for bioabsorbable drug carrier coatings
US20070173787A1 (en) * 2005-11-01 2007-07-26 Huang Mark C T Thin-film nitinol based drug eluting stent
JP5280852B2 (en) 2005-11-09 2013-09-04 シー・アール・バード・インコーポレーテッド Grafts and stent grafts with radiopaque markers
US8083983B2 (en) * 2005-11-28 2011-12-27 Rabolt John F Method of solution preparation of polyolefin class polymers for electrospinning processing included
US9446226B2 (en) * 2005-12-07 2016-09-20 Ramot At Tel-Aviv University Ltd. Drug-delivering composite structures
US20070155273A1 (en) * 2005-12-16 2007-07-05 Cornell Research Foundation, Inc. Non-woven fabric for biomedical application based on poly(ester-amide)s
US20070148365A1 (en) * 2005-12-28 2007-06-28 Knox David E Process and apparatus for coating paper
JP4778797B2 (en) * 2006-01-25 2011-09-21 株式会社Espinex Nanofiber
EP1974015A4 (en) * 2006-01-27 2012-07-04 Univ California Biomimetic scaffolds
US20080220042A1 (en) * 2006-01-27 2008-09-11 The Regents Of The University Of California Biomolecule-linked biomimetic scaffolds
US20070203564A1 (en) * 2006-02-28 2007-08-30 Boston Scientific Scimed, Inc. Biodegradable implants having accelerated biodegradation properties in vivo
US7737060B2 (en) * 2006-03-31 2010-06-15 Boston Scientific Scimed, Inc. Medical devices containing multi-component fibers
WO2008020326A2 (en) * 2006-04-07 2008-02-21 Victor Barinov Controlled electrospinning of fibers
US7689291B2 (en) * 2006-05-01 2010-03-30 Cardiac Pacemakers, Inc. Lead with fibrous matrix coating and methods related thereto
JP2008011942A (en) * 2006-07-03 2008-01-24 Univ Kansai Medical Medical tube
US20090127748A1 (en) * 2006-07-05 2009-05-21 Panasonic Corporation Method and apparatus for producing nanofibers and polymeric webs
EP2079575B1 (en) 2006-10-12 2021-06-02 C.R. Bard, Inc. Methods for making vascular grafts with multiple channels
US9492596B2 (en) 2006-11-06 2016-11-15 Atrium Medical Corporation Barrier layer with underlying medical device and one or more reinforcing support structures
US9622888B2 (en) 2006-11-16 2017-04-18 W. L. Gore & Associates, Inc. Stent having flexibly connected adjacent stent elements
JP4809203B2 (en) * 2006-12-13 2011-11-09 パナソニック株式会社 Nonwoven fabric manufacturing apparatus and nonwoven fabric manufacturing method
TW200848561A (en) * 2006-12-22 2008-12-16 Body Organ Biomedical Corp Device for manufacturing fibrils
CN101631813A (en) * 2007-01-12 2010-01-20 陶氏康宁公司 Silicone-containing composition
CA2676932C (en) 2007-02-01 2015-11-24 Technion Research & Development Foundation Ltd. Albumin fibers and fabrics and methods of generating and using same
US20080208325A1 (en) * 2007-02-27 2008-08-28 Boston Scientific Scimed, Inc. Medical articles for long term implantation
JP2008253297A (en) * 2007-03-30 2008-10-23 Univ Kansai Medical Medical tube
US20090042029A1 (en) * 2007-04-13 2009-02-12 Drexel University Polyamide nanofibers and methods thereof
US7993567B2 (en) * 2007-06-01 2011-08-09 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Method and system for aligning fibers during electrospinning
EP2160153A1 (en) * 2007-06-11 2010-03-10 Nanovasc, Inc. Stents
US20100331957A1 (en) * 2007-06-11 2010-12-30 Nanovasc, Inc. Implantable medical device
US20100070020A1 (en) * 2008-06-11 2010-03-18 Nanovasc, Inc. Implantable Medical Device
CA2692143C (en) * 2007-06-19 2015-07-07 Abdellah Ajji Non-woven mat and method of producing same
US20090004455A1 (en) * 2007-06-27 2009-01-01 Philippe Gravagna Reinforced composite implant
JP5142607B2 (en) * 2007-07-03 2013-02-13 兵庫県 Cover stent and manufacturing method thereof
US20090030504A1 (en) * 2007-07-27 2009-01-29 Boston Scientific Scimed, Inc. Medical devices comprising porous inorganic fibers for the release of therapeutic agents
ES2661762T3 (en) * 2007-10-10 2018-04-03 Wake Forest University Health Sciences Devices to treat spinal cord tissue
JP5476311B2 (en) * 2007-11-09 2014-04-23 イー・アイ・デュポン・ドウ・ヌムール・アンド・カンパニー Method of stripping solvent using antioxidant
US9308068B2 (en) 2007-12-03 2016-04-12 Sofradim Production Implant for parastomal hernia
US8926688B2 (en) 2008-01-11 2015-01-06 W. L. Gore & Assoc. Inc. Stent having adjacent elements connected by flexible webs
CA2718897A1 (en) * 2008-03-17 2009-09-17 The Board Of Regents Of The University Of Texas System Superfine fiber creating spinneret and uses thereof
US8252048B2 (en) * 2008-03-19 2012-08-28 Boston Scientific Scimed, Inc. Drug eluting stent and method of making the same
EP2291556A2 (en) * 2008-06-10 2011-03-09 Technion Research & Development Foundation Ltd. Nonwoven structure and method of fabricating the same
US9242026B2 (en) 2008-06-27 2016-01-26 Sofradim Production Biosynthetic implant for soft tissue repair
US8049061B2 (en) * 2008-09-25 2011-11-01 Abbott Cardiovascular Systems, Inc. Expandable member formed of a fibrous matrix having hydrogel polymer for intraluminal drug delivery
US8226603B2 (en) * 2008-09-25 2012-07-24 Abbott Cardiovascular Systems Inc. Expandable member having a covering formed of a fibrous matrix for intraluminal drug delivery
US8076529B2 (en) 2008-09-26 2011-12-13 Abbott Cardiovascular Systems, Inc. Expandable member formed of a fibrous matrix for intraluminal drug delivery
EP2962704A1 (en) 2008-10-07 2016-01-06 Nanonerve, Inc. Multilayer fibrous polymer scaffolds, methods of production and methods of use
KR101719377B1 (en) * 2008-10-17 2017-03-23 디킨 유니버시티 Electrostatic spinning assembly
US9427304B2 (en) * 2008-10-27 2016-08-30 St. Jude Medical, Cardiology Division, Inc. Multi-layer device with gap for treating a target site and associated method
US8178030B2 (en) 2009-01-16 2012-05-15 Zeus Industrial Products, Inc. Electrospinning of PTFE with high viscosity materials
US20130268062A1 (en) * 2012-04-05 2013-10-10 Zeus Industrial Products, Inc. Composite prosthetic devices
US9750829B2 (en) 2009-03-19 2017-09-05 Emd Millipore Corporation Removal of microorganisms from fluid samples using nanofiber filtration media
US8346374B2 (en) * 2009-07-09 2013-01-01 Cardiac Pacemakers, Inc. Laminate distal lead seal with tissue ingrowth feature
JP2013501539A (en) 2009-08-07 2013-01-17 ゼウス インダストリアル プロダクツ インコーポレイテッド Prosthetic device comprising an electrospun fiber layer and method for producing the same
US20110038910A1 (en) 2009-08-11 2011-02-17 Atrium Medical Corporation Anti-infective antimicrobial-containing biomaterials
FR2949688B1 (en) 2009-09-04 2012-08-24 Sofradim Production FABRIC WITH PICOTS COATED WITH A BIORESORBABLE MICROPOROUS LAYER
DE102009047925A1 (en) 2009-10-01 2011-06-16 Qualimed Innovative Medizinprodukte Gmbh Endoluminal tubular stent graft
US9005604B2 (en) * 2009-12-15 2015-04-14 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Aligned and electrospun piezoelectric polymer fiber assembly and scaffold
WO2011082295A2 (en) 2009-12-31 2011-07-07 Neograft Technologies, Inc. Graft devices and methods of fabrication
CZ303024B6 (en) * 2010-03-05 2012-02-29 Šafár@Václav Process for producing nanofibers by electrostatic spinning of polymeric solution and apparatus for making the same
WO2011119536A1 (en) 2010-03-22 2011-09-29 Abbott Cardiovascular Systems Inc. Stent delivery system having a fibrous matrix covering with improved stent retention
WO2011147409A2 (en) * 2010-05-27 2011-12-01 Hemoteq Ag Coating of endoprostheses with a coating consisting of a tight mesh of polymer fibres
EP3741896A1 (en) 2010-06-17 2020-11-25 Washington University Biomedical patches with aligned fibers
WO2012009707A2 (en) 2010-07-16 2012-01-19 Atrium Medical Corporation Composition and methods for altering the rate of hydrolysis of cured oil-based materials
WO2012021308A2 (en) 2010-08-10 2012-02-16 Millipore Corporation Method for retrovirus removal
EP2563956A4 (en) 2010-10-14 2013-09-18 Zeus Ind Products Inc Antimicrobial substrate
EP2646065A4 (en) 2010-12-05 2016-03-23 Nanonerve Inc Fibrous polymer scaffolds having diametrically patterned polymer fibers
KR101187212B1 (en) 2010-12-30 2012-10-02 주식회사 엠아이텍 Method for manufacturing drug eluting stent for benign biliary structure using electrospinning
JP6203639B2 (en) * 2011-01-28 2017-09-27 メリット・メディカル・システムズ・インコーポレイテッドMerit Medical Systems,Inc. Electrospun PTFE coated stent and method of use
US8658067B2 (en) 2011-02-07 2014-02-25 Fiberio Technology Corporation Apparatuses and methods for the deposition of microfibers and nanofibers on a substrate
DE102011012501A1 (en) * 2011-02-25 2012-08-30 Phenox Gmbh Implant with fiber fleece
FR2972626B1 (en) 2011-03-16 2014-04-11 Sofradim Production PROSTHETIC COMPRISING A THREE-DIMENSIONAL KNIT AND ADJUSTED
US10227568B2 (en) 2011-03-22 2019-03-12 Nanofiber Solutions, Llc Fiber scaffolds for use in esophageal prostheses
CN105413480B (en) 2011-04-01 2019-03-29 Emd密理博公司 Composite structure containing nanofiber
CZ2011376A3 (en) 2011-06-27 2012-08-22 Contipro Biotech S.R.O. Process for producing materials exhibiting anisotropic properties and composed of nanofibers or microfibers and apparatus for making the same
FR2977790B1 (en) 2011-07-13 2013-07-19 Sofradim Production PROSTHETIC FOR UMBILIC HERNIA
FR2977789B1 (en) 2011-07-13 2013-07-19 Sofradim Production PROSTHETIC FOR UMBILIC HERNIA
JP5665803B2 (en) * 2011-07-15 2015-02-04 クック メディカル テクノロジーズ エルエルシーCook Medical Technologies Llc Method for electrospinning a graft layer
CN102358959B (en) * 2011-08-16 2013-11-06 中山大学 Method and device for preparing electrospinning fiber bracket with three-dimensional structure
CN102973340A (en) * 2011-09-05 2013-03-20 上海市第十人民医院 Biodegradable cardia support
CN102973989A (en) * 2011-09-05 2013-03-20 上海市第十人民医院 Method for preparing surface fiber membrane of cardia stent
CN102973339A (en) * 2011-09-05 2013-03-20 上海市第十人民医院 Cardia stent with drug coating
WO2013046058A2 (en) 2011-09-30 2013-04-04 Sofradim Production Reversible stiffening of light weight mesh
US10239262B2 (en) 2011-11-21 2019-03-26 Nanofiber Solutions, Llc Fiber scaffolds for use in tracheal prostheses
FR2985170B1 (en) 2011-12-29 2014-01-24 Sofradim Production PROSTHESIS FOR INGUINAL HERNIA
DE102012008656A1 (en) * 2011-12-29 2013-07-04 Nonwotecc Medical Gmbh Structure with fibers glued together in places
FR2985271B1 (en) 2011-12-29 2014-01-24 Sofradim Production KNITTED PICOTS
US9884027B2 (en) 2012-01-12 2018-02-06 Nanofiber Solutions, Inc. Nanofiber scaffolds for biological structures
CN104114201A (en) 2012-01-16 2014-10-22 美国医疗设备有限公司 Rotational spun material covered medical appliances and methods of manufacture
CN104203151A (en) * 2012-02-14 2014-12-10 尼奥格拉夫特科技公司 Kink resistant graft devices and related systems and methods
PL231639B1 (en) 2012-04-17 2019-03-29 Politechnika Lodzka Medical material for the reconstruction of blood vessels, a method for producing the medical material and medical material applied to the reconstruction of blood vessels
US9867880B2 (en) 2012-06-13 2018-01-16 Atrium Medical Corporation Cured oil-hydrogel biomaterial compositions for controlled drug delivery
FR2994185B1 (en) 2012-08-02 2015-07-31 Sofradim Production PROCESS FOR THE PREPARATION OF A POROUS CHITOSAN LAYER
WO2014031950A1 (en) * 2012-08-24 2014-02-27 Herskovic Arnold M Device and method for improving brachytherapy
CN102784015B (en) * 2012-08-30 2015-06-03 广州迈普再生医学科技有限公司 Artificial blood vessel loaded with pseudo-ginseng medicines, and preparation method and application for artificial blood vessel
US20140081386A1 (en) * 2012-09-14 2014-03-20 Cook Medical Technologies Llc Endoluminal prosthesis
US10507268B2 (en) * 2012-09-19 2019-12-17 Merit Medical Systems, Inc. Electrospun material covered medical appliances and methods of manufacture
CA3066269C (en) 2012-09-21 2022-03-29 Washington University Multilayered biomedical structures configured to separate after a predetermined time or upon exposure to an environmental condition
US9198999B2 (en) 2012-09-21 2015-12-01 Merit Medical Systems, Inc. Drug-eluting rotational spun coatings and methods of use
FR2995778B1 (en) 2012-09-25 2015-06-26 Sofradim Production ABDOMINAL WALL REINFORCING PROSTHESIS AND METHOD FOR MANUFACTURING THE SAME
FR2995788B1 (en) 2012-09-25 2014-09-26 Sofradim Production HEMOSTATIC PATCH AND PREPARATION METHOD
FR2995779B1 (en) 2012-09-25 2015-09-25 Sofradim Production PROSTHETIC COMPRISING A TREILLIS AND A MEANS OF CONSOLIDATION
AU2013322268B2 (en) 2012-09-28 2017-08-31 Sofradim Production Packaging for a hernia repair device
US10582998B1 (en) * 2012-10-17 2020-03-10 Medshape, Inc. Shape memory polymer fabrics
US8992817B2 (en) * 2012-12-10 2015-03-31 Abbott Cardiovascular Systems, Inc. Process of making a medical balloon
US9091007B2 (en) * 2012-12-10 2015-07-28 Taipei Medical University Electrospinning apparatus with a sideway motion device and a method of using the same
US10154918B2 (en) 2012-12-28 2018-12-18 Cook Medical Technologies Llc Endoluminal prosthesis with fiber matrix
EP3988278A1 (en) 2013-03-13 2022-04-27 Merit Medical Systems, Inc. Serially deposited fiber materials and associated devices and methods
US9827703B2 (en) 2013-03-13 2017-11-28 Merit Medical Systems, Inc. Methods, systems, and apparatuses for manufacturing rotational spun appliances
US10660645B2 (en) 2013-03-15 2020-05-26 Embo Medical Limited Embolization systems
US10675039B2 (en) 2013-03-15 2020-06-09 Embo Medical Limited Embolisation systems
KR102333433B1 (en) 2013-03-15 2021-12-02 내셔널 유니버시티 오브 아일랜드, 갈웨이 Embolisation systems
US20140272225A1 (en) * 2013-03-15 2014-09-18 Nanofiber Solutions, Llc Biocompatible fiber textiles for implantation
FR3006581B1 (en) 2013-06-07 2016-07-22 Sofradim Production PROSTHESIS BASED ON TEXTILE FOR LAPAROSCOPIC PATHWAY
FR3006578B1 (en) 2013-06-07 2015-05-29 Sofradim Production PROSTHESIS BASED ON TEXTILE FOR LAPAROSCOPIC PATHWAY
CN103432631B (en) * 2013-06-26 2014-12-31 上海大学 Novel biodegradable vascular stent preparation method
CN103418023B (en) * 2013-07-29 2014-09-03 大连医科大学 Multilayer composite hemostatic material and preparation method thereof
WO2015048224A1 (en) * 2013-09-25 2015-04-02 Johnson Jed K Fiber scaffolds for use creating implantable structures
JP2015068986A (en) * 2013-09-27 2015-04-13 キヤノン株式会社 Manufacturing method of conductive member for electrophotography
KR101501383B1 (en) * 2013-10-30 2015-03-10 가톨릭대학교 산학협력단 Nanofiber scaffold with an aligned structure and method thereof
CA2931151C (en) * 2013-11-20 2022-02-15 Ryan Joaquin GERAKOPULOS Method and system for forming composites
US9814560B2 (en) 2013-12-05 2017-11-14 W. L. Gore & Associates, Inc. Tapered implantable device and methods for making such devices
EP3086741A4 (en) * 2013-12-27 2018-01-03 Neograft Technologies, Inc. Artificial graft devices and related systems and methods
WO2015127254A1 (en) * 2014-02-21 2015-08-27 Healionics Corporation Vascular grafts and method for preserving patency of same
US9675361B2 (en) 2014-02-28 2017-06-13 Cook Medical Technologies Llc Coil occlusion device
EP3000489B1 (en) 2014-09-24 2017-04-05 Sofradim Production Method for preparing an anti-adhesion barrier film
EP3000432B1 (en) 2014-09-29 2022-05-04 Sofradim Production Textile-based prosthesis for treatment of inguinal hernia
EP3000433B1 (en) 2014-09-29 2022-09-21 Sofradim Production Device for introducing a prosthesis for hernia treatment into an incision and flexible textile based prosthesis
CN104383606B (en) * 2014-10-27 2016-02-17 北京航空航天大学 A kind of high-strength high-elasticity intravascular stent and preparation method thereof
US10299948B2 (en) 2014-11-26 2019-05-28 W. L. Gore & Associates, Inc. Balloon expandable endoprosthesis
EP3029189B1 (en) 2014-12-05 2021-08-11 Sofradim Production Prosthetic porous knit, method of making same and hernia prosthesis
US20160175082A1 (en) * 2014-12-23 2016-06-23 Novus Scientific Ab Resorbable medical mesh implant for repair or prevention of parastomal hernia
EP3059255B1 (en) 2015-02-17 2020-05-13 Sofradim Production Method for preparing a chitosan-based matrix comprising a fiber reinforcement member
US10028852B2 (en) 2015-02-26 2018-07-24 Merit Medical Systems, Inc. Layered medical appliances and methods
JP6974916B2 (en) * 2015-02-27 2021-12-01 ユニバーシティ オブ ピッツバーグ − オブ ザ コモンウェルス システム オブ ハイヤー エデュケイション Dual component mandrel for electrospun stentless fabrication of multi-valve valve
WO2016138423A1 (en) 2015-02-27 2016-09-01 University Of Pittsburgh - Of The Commonwealth System Of Higher Education Retrievable self-expanding non-thrombogenic low-profile percutaneous atrioventricular valve prosthesis
FR3033494B1 (en) * 2015-03-10 2017-03-24 Carmat TISSUE STENT AND METHOD FOR PRODUCING THE SAME
CN104713909A (en) * 2015-04-10 2015-06-17 湖南农业大学 Simple method for authenticating fluorine injury of plants
SG11201706726TA (en) 2015-04-17 2017-09-28 Emd Millipore Corp Method of purifying a biological materia of interest in a sample using nanofiber ultrafiltration membranes operated in tangential flow filtration mode
EP3085337B1 (en) 2015-04-24 2022-09-14 Sofradim Production Prosthesis for supporting a breast structure
US10166315B2 (en) 2015-05-04 2019-01-01 Nanofiber Solutions, Inc. Chitosan-enhanced electrospun fiber compositions
BR112017025950A2 (en) 2015-06-05 2018-08-14 W. L. Gore & Associates, Inc. ? low bleed implantable prosthesis with a taper?
ES2676072T3 (en) 2015-06-19 2018-07-16 Sofradim Production Synthetic prosthesis comprising a knitted fabric and a non-porous film and method of forming it
CN105113029A (en) * 2015-09-23 2015-12-02 厦门大学 Linear nozzle for electrostatic spinning
ES2913723T3 (en) * 2015-10-01 2022-06-06 Xeltis Ag Methods of coating and lamination of endoluminal prostheses by electrospinning
WO2017070147A1 (en) 2015-10-23 2017-04-27 Boston Scientific Scimed, Inc. Radioactive stents
US10953097B2 (en) 2015-11-02 2021-03-23 Nanofiber Solutions. Llc Electrospun fibers having contrast agents and methods of making the same
EP3400132A4 (en) * 2016-01-08 2019-08-07 Clarcor Inc. Use of microfibers and/or nanofibers in apparel and footwear
EP3195830B1 (en) 2016-01-25 2020-11-18 Sofradim Production Prosthesis for hernia repair
EP3426315A1 (en) * 2016-03-11 2019-01-16 The Johns Hopkins University Partially degradable stents for controlled reduction of intraocular pressure
KR101795923B1 (en) * 2016-04-15 2017-11-10 연세대학교 산학협력단 Stent for releasing nano-particle including biodegradable polymer, hydrophilic drug and hydrophobic drug
US10632228B2 (en) 2016-05-12 2020-04-28 Acera Surgical, Inc. Tissue substitute materials and methods for tissue repair
US10568752B2 (en) 2016-05-25 2020-02-25 W. L. Gore & Associates, Inc. Controlled endoprosthesis balloon expansion
CN106319647A (en) * 2016-10-21 2017-01-11 上海工程技术大学 Method for preparing nanofiber aggregate and pretreatment device
EP3312325B1 (en) 2016-10-21 2021-09-22 Sofradim Production Method for forming a mesh having a barbed suture attached thereto and the mesh thus obtained
US10898608B2 (en) 2017-02-02 2021-01-26 Nanofiber Solutions, Llc Methods of improving bone-soft tissue healing using electrospun fibers
US10368991B2 (en) * 2017-02-06 2019-08-06 C. R. Bard, Inc. Device and associated percutaneous minimally invasive method for creating a venous valve
EP3398554A1 (en) 2017-05-02 2018-11-07 Sofradim Production Prosthesis for inguinal hernia repair
GB201708025D0 (en) * 2017-05-18 2017-07-05 Clearstream Tech Ltd A laminate membrane, an implant comprising the laminate membrane and a method of manufacturing the same
TW201904527A (en) * 2017-06-23 2019-02-01 鴻海精密工業股份有限公司 Artificial blood vessel and method for making the same
EP3427764A1 (en) 2017-07-12 2019-01-16 Université de Technologie de Compiègne Fibrous polymer material comprising fibroin and polymer scaffolds comprising thereof
CA3074944A1 (en) 2017-09-08 2019-03-14 Board Of Regents Of The University Of Texas System Mechanoluminescence polymer doped fabrics and methods of making
NL2019763B1 (en) * 2017-10-19 2019-04-29 Innovative Mechanical Engineering Tech B V Electro hydrodynamic production method and system
CN112203616A (en) * 2017-10-30 2021-01-08 安多拉米诺科学公司 Expandable sealing skirt technique for leak-proof endovascular prosthesis
US11174570B2 (en) 2018-02-05 2021-11-16 Fermi Research Alliance, Llc Methods and systems for electrospinning using low power voltage converter
GB2573092A (en) * 2018-03-02 2019-10-30 The Electrospinning Company Ltd Porous scaffold for the delivery of therapeutic agents
CN110512292B (en) * 2018-05-21 2023-02-17 武汉纺织大学 Radial electrospinning nozzle based on rectangular blades
CZ309078B6 (en) 2018-05-28 2022-01-19 Contipro A.S. Device and method of producing nano- and / or microfibrous layers with increased thickness uniformity
CN108939267B (en) * 2018-05-28 2021-04-16 苏州大学 Controlled drug release device and method
CN109248340B (en) * 2018-09-18 2021-04-23 武汉纺织大学 Preparation method of fiber-based artificial blood vessel
EP3653171A1 (en) 2018-11-16 2020-05-20 Sofradim Production Implants suitable for soft tissue repair
TW202031958A (en) * 2018-12-05 2020-09-01 奧地利商蘭仁股份有限公司 Method and device for producing tubular cellulosic spunbonded nonwoven fabrics
DE102018131269B4 (en) 2018-12-07 2021-08-05 Acandis Gmbh Medical device for insertion into a hollow body organ and manufacturing process
JP2022513442A (en) 2018-12-11 2022-02-08 ナノファイバー ソリューションズ、エルエルシー How to treat chronic wounds using electrospun fibers
WO2020165906A1 (en) * 2019-02-14 2020-08-20 Technion Research & Development Foundation Limited Composition, drug delivery device and method for local delivery of an active agent
US11427937B2 (en) 2019-02-20 2022-08-30 The Board Of Regents Of The University Of Texas System Handheld/portable apparatus for the production of microfibers, submicron fibers and nanofibers
CN110067080B (en) * 2019-03-07 2021-05-25 江苏大学 Janus infrared radiation film for human body heat preservation and preparation method thereof
CN109908401A (en) * 2019-03-11 2019-06-21 武汉杨森生物技术有限公司 A kind of production method of artificial blood vessel and products thereof for promoting endothelial cell to seek connections with
CN110215540B (en) * 2019-04-09 2021-07-27 盐城工业职业技术学院 Silk fibroin/polymer based tubular stent with three-dimensional ordered and disordered double-network structure and preparation and use methods thereof
US20220228296A1 (en) * 2019-05-30 2022-07-21 Jack L. Skinner Device for polymer materials fabrication using gas flow and electrostatic fields
CN110141760B (en) * 2019-06-05 2021-10-08 山东百多安医疗器械股份有限公司 Centrum forming expansion balloon with drug loaded on surface and preparation method thereof
DE102019121559A1 (en) * 2019-08-09 2021-02-11 Acandis Gmbh Medical device for insertion into a hollow body organ and method for producing a medical device
DE102019121562B4 (en) 2019-08-09 2024-01-11 Acandis Gmbh Medical device for treating aneurysms
US20220331088A1 (en) * 2019-09-04 2022-10-20 SB-Kawasumi Laboratories, Inc. Membrane body for tubular treatment device and tubular treatment device
CN110743033B (en) * 2019-10-23 2021-12-28 辽宁燕阳医疗设备有限公司 Medical dressing
TWI749395B (en) * 2019-11-08 2021-12-11 高鼎精密材料股份有限公司 Method for fabricating polymer fiber tubular structure with high patency rate
DE102019135502B4 (en) * 2019-12-20 2022-07-14 Acandis Gmbh Medical set, medical system and covering device for the treatment of aneurysms
CN111139541B (en) * 2020-03-10 2023-06-30 苏州大学 Stirring type large-batch free liquid level electrostatic spinning device and method
CN214712943U (en) * 2020-09-30 2021-11-16 普利瑞医疗科技(苏州)有限公司 Medical drug stent
CN114176597A (en) * 2021-12-17 2022-03-15 广东思谷智能技术有限公司 All-electric spinning high-air-permeability high-hydrophobicity friction nano sensor and preparation method thereof

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3860369A (en) * 1972-11-02 1975-01-14 Du Pont Apparatus for making non-woven fibrous sheet
US4689186A (en) * 1978-10-10 1987-08-25 Imperial Chemical Industries Plc Production of electrostatically spun products

Family Cites Families (107)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2491889A (en) * 1942-01-21 1949-12-20 Owens Corning Fiberglass Corp Production of coated glass and the like products
US3280229A (en) * 1963-01-15 1966-10-18 Kendall & Co Process and apparatus for producing patterned non-woven fabrics
CH472219A (en) 1963-06-15 1969-05-15 Spofa Vereinigte Pharma Werke Highly porous collagen tissue blood vessel prosthesis and method for producing the same
US3625745A (en) 1970-03-18 1971-12-07 Gen Electric Antithrombogenic article and process
US3688317A (en) 1970-08-25 1972-09-05 Sutures Inc Vascular prosthetic
GB1527592A (en) 1974-08-05 1978-10-04 Ici Ltd Wound dressing
FR2382688A1 (en) 1977-03-04 1978-09-29 Oreal HARDNESS MEASURING DEVICE
DE2960875D1 (en) * 1978-04-19 1981-12-10 Ici Plc A method of preparing a tubular product by electrostatic spinning
US4223101A (en) 1978-07-17 1980-09-16 Inmont Corporation Method of producing fibrous structure
EP0011437B1 (en) 1978-11-20 1983-06-22 Imperial Chemical Industries Plc A process for setting a product comprising electrostatically spun fibres, and products prepared according to this process
FI70586C (en) 1979-05-03 1986-09-24 Le I Textilnoi POROEST FYLLMEDELINNEHAOLLANDE REACTIVE MATERIAL VID OEPPNA CELER OCH FOERFARANDE FOER FRAMSTAELLNING AV DETTA
FR2511014B1 (en) * 1981-08-10 1987-02-06 Ethicon Inc PROCESS FOR THE PREPARATION OF A POLYURETHANE RESIN SUITABLE FOR ELECTROSTATIC SPINNING
US4475972A (en) * 1981-10-01 1984-10-09 Ontario Research Foundation Implantable material
GB2142870B (en) * 1983-07-06 1986-06-04 Ethicon Inc Manufacturing vascular prostheses by electrostatic spinning
US4759757A (en) 1984-04-18 1988-07-26 Corvita Corporation Cardiovascular graft and method of forming same
US4657793A (en) 1984-07-16 1987-04-14 Ethicon, Inc. Fibrous structures
US5679967A (en) * 1985-01-20 1997-10-21 Chip Express (Israel) Ltd. Customizable three metal layer gate array devices
US4798606A (en) 1985-02-26 1989-01-17 Corvita Corporation Reinforcing structure for cardiovascular graft
US4880002A (en) 1985-05-30 1989-11-14 Corvita Corporation Stretchable porous sutures
GB2181207B (en) * 1985-10-04 1990-05-23 Ethicon Inc Improvements in electrostatically produced structures and methods of manufacturing thereof
US4738740A (en) * 1985-11-21 1988-04-19 Corvita Corporation Method of forming implantable vascular grafts
US4739013A (en) 1985-12-19 1988-04-19 Corvita Corporation Polyurethanes
US4743252A (en) 1986-01-13 1988-05-10 Corvita Corporation Composite grafts
GB2189738B (en) 1986-03-24 1989-11-15 Ethicon Inc Apparatus for producing fibrous structures electrostatically
GB8617527D0 (en) 1986-07-17 1986-08-28 Ici Plc Spraying process
US4802145A (en) 1986-08-01 1989-01-31 Amoco Corporation Method and apparatus for determining cement conditions
US5084085A (en) 1986-08-20 1992-01-28 Fmc Corporation Herbicidal aryloxyphenyltriazolinones and related compounds
US4769030A (en) 1987-04-28 1988-09-06 Corvita Corporation Monomer and use thereof in crack prevention of implanted prostheses
US4872455A (en) 1987-11-25 1989-10-10 Corvita Corporation Anastomosis trimming device and method of using the same
US4997600A (en) * 1988-05-24 1991-03-05 Mitsubishi Monsanto Chemical Company, Ltd. Process for preparation of thermoplastic resin sheets
US4965110A (en) 1988-06-20 1990-10-23 Ethicon, Inc. Electrostatically produced structures and methods of manufacturing
US5226913A (en) 1988-09-01 1993-07-13 Corvita Corporation Method of making a radially expandable prosthesis
US5092877A (en) 1988-09-01 1992-03-03 Corvita Corporation Radially expandable endoprosthesis
US5019090A (en) 1988-09-01 1991-05-28 Corvita Corporation Radially expandable endoprosthesis and the like
US4904174A (en) * 1988-09-15 1990-02-27 Peter Moosmayer Apparatus for electrically charging meltblown webs (B-001)
US5024671A (en) 1988-09-19 1991-06-18 Baxter International Inc. Microporous vascular graft
US5024789A (en) * 1988-10-13 1991-06-18 Ethicon, Inc. Method and apparatus for manufacturing electrostatically spun structure
US5298255A (en) 1988-10-28 1994-03-29 Terumo Kabushiki Kaisha Antithrombic medical material, artificial internal organ, and method for production of antithrombic medical material
US4905367A (en) 1988-11-08 1990-03-06 Corvita Corporation Manufacture of stretchable porous sutures
US4990158A (en) 1989-05-10 1991-02-05 United States Surgical Corporation Synthetic semiabsorbable tubular prosthesis
US5084065A (en) 1989-07-10 1992-01-28 Corvita Corporation Reinforced graft assembly
US6004346A (en) 1990-02-28 1999-12-21 Medtronic, Inc. Intralumenal drug eluting prosthesis
US5545208A (en) 1990-02-28 1996-08-13 Medtronic, Inc. Intralumenal drug eluting prosthesis
CA2038605C (en) 1990-06-15 2000-06-27 Leonard Pinchuk Crack-resistant polycarbonate urethane polymer prostheses and the like
US5147725A (en) 1990-07-03 1992-09-15 Corvita Corporation Method for bonding silicone rubber and polyurethane materials and articles manufactured thereby
US6117425A (en) 1990-11-27 2000-09-12 The American National Red Cross Supplemented and unsupplemented tissue sealants, method of their production and use
US5116360A (en) 1990-12-27 1992-05-26 Corvita Corporation Mesh composite graft
GB9115276D0 (en) 1991-07-15 1991-08-28 Unilever Plc Skin treatment system
US5376117A (en) 1991-10-25 1994-12-27 Corvita Corporation Breast prostheses
US5599352A (en) 1992-03-19 1997-02-04 Medtronic, Inc. Method of making a drug eluting stent
US5383928A (en) 1992-06-10 1995-01-24 Emory University Stent sheath for local drug delivery
BE1006440A3 (en) 1992-12-21 1994-08-30 Dereume Jean Pierre Georges Em Luminal endoprosthesis AND METHOD OF PREPARATION.
US5419760A (en) 1993-01-08 1995-05-30 Pdt Systems, Inc. Medicament dispensing stent for prevention of restenosis of a blood vessel
EP0623941B1 (en) 1993-03-09 1997-08-06 Hoechst Celanese Corporation Polymer electrets with improved charge stability
US5334201A (en) 1993-03-12 1994-08-02 Cowan Kevin P Permanent stent made of a cross linkable material
US5383922A (en) 1993-03-15 1995-01-24 Medtronic, Inc. RF lead fixation and implantable lead
WO1994021308A1 (en) 1993-03-18 1994-09-29 Cedars-Sinai Medical Center Drug incorporating and releasing polymeric coating for bioprosthesis
US5824048A (en) 1993-04-26 1998-10-20 Medtronic, Inc. Method for delivering a therapeutic substance to a body lumen
US5464650A (en) 1993-04-26 1995-11-07 Medtronic, Inc. Intravascular stent and method
US5360397A (en) 1993-07-02 1994-11-01 Corvita Corporation Hemodiaylsis catheter and catheter assembly
DE4327595A1 (en) 1993-08-17 1995-02-23 Hoechst Ag Compositions with improved electrostatic properties containing aromatic polyamides, molded articles made therefrom and their use and process for their production
US5632772A (en) 1993-10-21 1997-05-27 Corvita Corporation Expandable supportive branched endoluminal grafts
US5723004A (en) 1993-10-21 1998-03-03 Corvita Corporation Expandable supportive endoluminal grafts
US5639278A (en) 1993-10-21 1997-06-17 Corvita Corporation Expandable supportive bifurcated endoluminal grafts
US5855598A (en) 1993-10-21 1999-01-05 Corvita Corporation Expandable supportive branched endoluminal grafts
US5549663A (en) 1994-03-09 1996-08-27 Cordis Corporation Endoprosthesis having graft member and exposed welded end junctions, method and procedure
US5415664A (en) 1994-03-30 1995-05-16 Corvita Corporation Method and apparatus for introducing a stent or a stent-graft
US6001123A (en) 1994-04-01 1999-12-14 Gore Enterprise Holdings Inc. Folding self-expandable intravascular stent-graft
EP0689805B1 (en) 1994-06-27 2003-05-28 Corvita Corporation Bistable luminal graft endoprostheses
US5629077A (en) 1994-06-27 1997-05-13 Advanced Cardiovascular Systems, Inc. Biodegradable mesh and film stent
DE9414040U1 (en) 1994-08-30 1995-01-19 Hoechst Ag Nonwovens made from electret fiber blends with improved charge stability
EP0761251B1 (en) 1994-10-17 2004-12-29 Kabushikikaisha Igaki Iryo Sekkei Drug-releasing stent
US5637113A (en) 1994-12-13 1997-06-10 Advanced Cardiovascular Systems, Inc. Polymer film for wrapping a stent structure
US5755722A (en) 1994-12-22 1998-05-26 Boston Scientific Corporation Stent placement device with medication dispenser and method
US5575818A (en) 1995-02-14 1996-11-19 Corvita Corporation Endovascular stent with locking ring
EP0810845A2 (en) 1995-02-22 1997-12-10 Menlo Care Inc. Covered expanding mesh stent
US6579314B1 (en) * 1995-03-10 2003-06-17 C.R. Bard, Inc. Covered stent with encapsulated ends
BE1009277A3 (en) 1995-04-12 1997-01-07 Corvita Europ Guardian self-expandable medical device introduced in cavite body, and method of preparation.
BE1009278A3 (en) 1995-04-12 1997-01-07 Corvita Europ Guardian self-expandable medical device introduced in cavite body, and medical device with a stake as.
US5700269A (en) 1995-06-06 1997-12-23 Corvita Corporation Endoluminal prosthesis deployment device for use with prostheses of variable length and having retraction ability
US5609629A (en) 1995-06-07 1997-03-11 Med Institute, Inc. Coated implantable medical device
AU716005B2 (en) 1995-06-07 2000-02-17 Cook Medical Technologies Llc Implantable medical device
US6023170A (en) 1995-06-08 2000-02-08 Instituut Voor Milieu- En Agritechniek Method for determining the degree of hardening of a material
US5627368A (en) 1995-07-05 1997-05-06 Gas Research Institute Four-detector formation-density tool for use in cased and open holes
US5628788A (en) 1995-11-07 1997-05-13 Corvita Corporation Self-expanding endoluminal stent-graft
US5800512A (en) 1996-01-22 1998-09-01 Meadox Medicals, Inc. PTFE vascular graft
US5749921A (en) 1996-02-20 1998-05-12 Medtronic, Inc. Apparatus and methods for compression of endoluminal prostheses
CA2199890C (en) 1996-03-26 2002-02-05 Leonard Pinchuk Stents and stent-grafts having enhanced hoop strength and methods of making the same
US6252129B1 (en) 1996-07-23 2001-06-26 Electrosols, Ltd. Dispensing device and method for forming material
US5741331A (en) 1996-07-29 1998-04-21 Corvita Corporation Biostable elastomeric polymers having quaternary carbons
US5797887A (en) 1996-08-27 1998-08-25 Novovasc Llc Medical device with a surface adapted for exposure to a blood stream which is coated with a polymer containing a nitrosyl-containing organo-metallic compound which releases nitric oxide from the coating to mediate platelet aggregation
SE509834C2 (en) 1996-09-09 1999-03-15 Bandak As Filter element for pressure filter
IL119809A (en) 1996-12-11 2001-06-14 Nicast Ltd Device for manufacture of composite filtering material and method of its manufacture
US5980972A (en) 1996-12-20 1999-11-09 Schneider (Usa) Inc Method of applying drug-release coatings
US5980551A (en) 1997-02-07 1999-11-09 Endovasc Ltd., Inc. Composition and method for making a biodegradable drug delivery stent
US5843172A (en) 1997-04-15 1998-12-01 Advanced Cardiovascular Systems, Inc. Porous medicated stent
US6371982B2 (en) 1997-10-09 2002-04-16 St. Jude Medical Cardiovascular Group, Inc. Graft structures with compliance gradients
US6106913A (en) * 1997-10-10 2000-08-22 Quantum Group, Inc Fibrous structures containing nanofibrils and other textile fibers
US5938697A (en) 1998-03-04 1999-08-17 Scimed Life Systems, Inc. Stent having variable properties
US6019789A (en) 1998-04-01 2000-02-01 Quanam Medical Corporation Expandable unit cell and intraluminal stent
US6013099A (en) 1998-04-29 2000-01-11 Medtronic, Inc. Medical device for delivering a water-insoluble therapeutic salt or substance
US6265333B1 (en) * 1998-06-02 2001-07-24 Board Of Regents, University Of Nebraska-Lincoln Delamination resistant composites prepared by small diameter fiber reinforcement at ply interfaces
US20020081732A1 (en) * 2000-10-18 2002-06-27 Bowlin Gary L. Electroprocessing in drug delivery and cell encapsulation
US6306424B1 (en) 1999-06-30 2001-10-23 Ethicon, Inc. Foam composite for the repair or regeneration of tissue
US6682004B2 (en) * 1999-08-18 2004-01-27 The Procter & Gamble Company Electrostatic spray device
US6270793B1 (en) 1999-09-13 2001-08-07 Keraplast Technologies, Ltd. Absorbent keratin wound dressing
US20020084178A1 (en) * 2000-12-19 2002-07-04 Nicast Corporation Ltd. Method and apparatus for manufacturing polymer fiber shells via electrospinning

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3860369A (en) * 1972-11-02 1975-01-14 Du Pont Apparatus for making non-woven fibrous sheet
US4689186A (en) * 1978-10-10 1987-08-25 Imperial Chemical Industries Plc Production of electrostatically spun products

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP1355677A2 *

Cited By (24)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2004256973A (en) * 2003-02-27 2004-09-16 Japan Vilene Co Ltd Method for electrospinning and device for electrospinning
JP2004256974A (en) * 2003-02-27 2004-09-16 Japan Vilene Co Ltd Method for electrospinning and device for electrospinning
WO2005042813A1 (en) * 2003-10-30 2005-05-12 Clean Air Technology Corp. Electrostatic spinning equipment and method of preparing nano fiber using the same
WO2005064048A1 (en) * 2003-12-30 2005-07-14 Raisio Chemicals Korea Inc. A method manufacturing nano-fibers with excellent fiber formation
WO2005095684A1 (en) * 2004-03-25 2005-10-13 Massachusetts Institute Of Technology Production of submicron diameter fibers by two-fluid electrospinning process
US8088324B2 (en) 2004-04-08 2012-01-03 Research Triangle Institute Electrospray/electrospinning apparatus and method
US7762801B2 (en) 2004-04-08 2010-07-27 Research Triangle Institute Electrospray/electrospinning apparatus and method
US8632721B2 (en) 2004-04-08 2014-01-21 Research Triangle Institute Electrospinning in a controlled gaseous environment
US7297305B2 (en) 2004-04-08 2007-11-20 Research Triangle Institute Electrospinning in a controlled gaseous environment
US8052407B2 (en) 2004-04-08 2011-11-08 Research Triangle Institute Electrospinning in a controlled gaseous environment
US7134857B2 (en) 2004-04-08 2006-11-14 Research Triangle Institute Electrospinning of fibers using a rotatable spray head
US7592277B2 (en) 2005-05-17 2009-09-22 Research Triangle Institute Nanofiber mats and production methods thereof
US8425810B2 (en) 2009-02-05 2013-04-23 Panasonic Corporation Nanofiber production device and nanofiber production method
WO2011048206A1 (en) * 2009-10-22 2011-04-28 Gyeong-Man Kim Anti-migration casing for transponders
EP2314739A1 (en) * 2009-10-22 2011-04-27 Gyeong-Man Kim Anti-migration casing for transponders
US10307292B2 (en) 2011-07-18 2019-06-04 Mor Research Applications Ltd Device for adjusting the intraocular pressure
WO2016199139A1 (en) 2015-06-08 2016-12-15 Corneat Vision Ltd Keratoprosthesis and uses thereof
US10667902B2 (en) 2015-06-08 2020-06-02 Corneat Vision Ltd Keratoprosthesis and uses thereof
US11213382B2 (en) 2015-06-08 2022-01-04 Corneat Vision Ltd Keratoprosthesis and uses thereof
WO2018081554A1 (en) * 2016-10-27 2018-05-03 North Carolina State University 3d printing of fibrous structures
WO2019234741A1 (en) 2018-06-05 2019-12-12 Corneat Vision Ltd. A synthetic ophthalmic graft patch
WO2020217244A1 (en) 2019-04-25 2020-10-29 Corneat Vision Ltd. Keratoprosthesis devices and kits and surgical methods of their use
WO2021028912A1 (en) 2019-08-12 2021-02-18 Corneat Vision Ltd. Gingival graft
WO2023161945A1 (en) 2022-02-27 2023-08-31 Corneat Vision Ltd. Implantable sensor

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CA2432164A1 (en) 2002-06-27
US7115220B2 (en) 2006-10-03
JP2004532665A (en) 2004-10-28
EP1578306A2 (en) 2005-09-28
DE60141710D1 (en) 2010-05-12
EP1355677A4 (en) 2004-05-26
US20020084178A1 (en) 2002-07-04
CA2432159A1 (en) 2002-06-27
WO2002049535A2 (en) 2002-06-27
JP4145143B2 (en) 2008-09-03
MXPA03005552A (en) 2003-10-24
IL156513A (en) 2008-04-13
US7112293B2 (en) 2006-09-26
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US20040053553A1 (en) 2004-03-18
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JP2005507464A (en) 2005-03-17
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HK1080347A1 (en) 2006-04-28
IL156513A0 (en) 2004-01-04
IL156514A (en) 2009-11-18
US20040096533A1 (en) 2004-05-20
CA2432164C (en) 2010-01-26
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