EP0261200A1 - Protheses vasculaires et procede de fabrication - Google Patents

Protheses vasculaires et procede de fabrication

Info

Publication number
EP0261200A1
EP0261200A1 EP87902220A EP87902220A EP0261200A1 EP 0261200 A1 EP0261200 A1 EP 0261200A1 EP 87902220 A EP87902220 A EP 87902220A EP 87902220 A EP87902220 A EP 87902220A EP 0261200 A1 EP0261200 A1 EP 0261200A1
Authority
EP
European Patent Office
Prior art keywords
vascular prosthesis
tubular segment
thin
accordance
line binder
Prior art date
Legal status (The legal status 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 status listed.)
Withdrawn
Application number
EP87902220A
Other languages
German (de)
English (en)
Inventor
Steven L. Weinberg
Roger W. Snyder
Gabriel P. Lalor
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Advanced Vascular Technologies LLC
Original Assignee
Advanced Vascular Technologies LLC
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
Application filed by Advanced Vascular Technologies LLC filed Critical Advanced Vascular Technologies LLC
Publication of EP0261200A1 publication Critical patent/EP0261200A1/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS 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
    • A61F2/00—Filters 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
    • A61F2/02—Prostheses implantable into the body
    • A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06—Blood vessels
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS 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
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/28—Materials for coating prostheses
    • A61L27/34—Macromolecular materials
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L23/00—Compositions of homopolymers or copolymers of unsaturated aliphatic hydrocarbons having only one carbon-to-carbon double bond; Compositions of derivatives of such polymers
    • C08L23/02—Compositions of homopolymers or copolymers of unsaturated aliphatic hydrocarbons having only one carbon-to-carbon double bond; Compositions of derivatives of such polymers not modified by chemical after-treatment
    • C08L23/10—Homopolymers or copolymers of propene
    • C08L23/12—Polypropene
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L67/00—Compositions of polyesters obtained by reactions forming a carboxylic ester link in the main chain; Compositions of derivatives of such polymers

Definitions

  • This invention pertains to vascular prostheses and particularly to stabilizing vascular prostheses to render them non-fraying, resistant to suture pullout and resistant to dilation, all without otherwise damaging their other properties.
  • Such prostheses have been employed in vascular surgery for the replacement and by-pass of arteries for about 30 years.
  • Such prostheses are generally tubular in shape; made of polyester, especially polyethylene terephthalate (e.g., DacrorP) or TeflorP, especially polytetrafluoroethylene, material; are either woven or knitted; and are crimped to provide resistance to kinking and to permit some elongation or stretching by the surgeon at the critical time of performing the surgery.
  • Such tubular prostheses are constructed in several shapes, typically straight, bifurcated and tapered.
  • Typical fabric constructions that are employed include a plain warp/weft interlaced weave, a plush weave known as a velour weave (wherein an extra thread or filament is included which is interlaced or "floats" over a plurality of threads in the opposite orientation or direction to add plushness to one or both the internal and external surface of the graft) and a knit (wherein single or multiple threads are interlaced with respect to themselves in a regular interlocking pattern) .
  • the threads or filaments used in the construction of vascu ⁇ lar prostheses have been flat, texturized and single or multiple ply and have been round and trilobal in cross- section.
  • Tube sizes for textile based artificial vascular grafts vary from about 4 mm internal diameter to about 35 mm. They vary in "porosity" (actually, in water permeability) from about 50-1500 ml/min/cm 2 for woven grafts and from about 1000-4000 ml/min/cm 2 for knitted grafts.
  • the nominal wall thickness of the materials vary from about 0.5 mm to about 1.5 mm.
  • Crimping dimension varies from about 2.0 mm for some knit grafts to a dimension under 0.5 mm for some woven grafts. Crimping is normally provided in a helix or spiral pattern or a circular pattern.
  • Some vascular prostheses in the past have also included reinforcement spiral and circular rings or loops, particularly at locations where the anticipated use indicates a bend or turn in the tubular material, thereby subjecting the material to the danger of possible kinking or compression.
  • Such rings or loops are slipped over the outside of the tube. They are usually of an appreciable dimension, on the order of 0.6-1.2 mm in diameter, and are applied as individual rings spaced along the length or as loops of a spiral wrap. They may or may not be permanently fixedly secured to the tube.
  • the number of rings or spiral loops employed has no relation to the number of crimpings, there usually being only two or three rings or loops per linear inch of tube, whereas there may be a dozen or more crimps per linear inch.
  • Such rings or loops employed in the past have been employed with respect to both crimped and uncrimped prostheses.
  • the vascular prostheses employed in the past have had three related shortcomings.
  • the stock which comes in relatively long lengths, are cut and trimmed for a particular application.
  • the end frequently frays.
  • the particularly aggravating propensity to fray or pullout when the material is sutured near the cut end of the tube. Because of this propensity, surgeons do not suture as near to the ends as they would otherwise prefer.
  • knitted grafts in the past have had a propensity to diliate or gradually open up or expand in one or more directions over a period of time. Such propensity can even result in hemorrhaging.
  • an improved vascular prosthesis including a thin in-line binder secured to the interstices of the tubular segment to reduce the propensity , of the tubular segment from fraying, to increase the suture holding capability of the prosthesis and to virtually eliminate harmful dilation, all without appreciable loss in porosity handling.
  • a woven and spirally or helically crimped vascular prosthesis is provided in a preferred manufactur ⁇ ing procedure with a very thin polypropylene monofilament which is wrapped in the root of the crimps.
  • the monofila ⁇ ment has a diameter less than the root-to-crest diameter of the material. It is heated at a temperature that is just enough to soften the monofilament without melting or burning the substrate or base tubular material, the softened monofilament material fusing with the external surface fibers of the tubular material. Hence, the monofilament becomes an overlaid or integral thin-line binder.
  • the external feel of the tube does not change since the monofilament is entirely confined within the helical groove of the crimp.
  • the addition of the softened monofilament does not interfere with the elongation or the elasticity provided by the crimping nor does it appreciably affect the porosity.
  • Alterna ⁇ tive means to a melted monofilament are also available to provide a similar non-fraying overlaid and involved structure, such as by spraying and by gluing.
  • a thin-line binder that is not related to the crimping structure, which is particularly useful for tubular vascular grafts that are circularly crimped, rather than spirally crimped, which is often employed with knit grafts.
  • Thin-line binders can be laid axially, helically or in a double helical pattern prior to crimping or with respect to a graft that is left uncrimped. In either of such cases the added thin-line binder is not confined to a crimp groove at all, but the dimension is small enough not to appreciably change the feel or appearance of the knitted surface. It should be noted that knitted and velour surfaces are usually more textured and porous than a woven surface, and, therefore, more forgiving in this regard.
  • the monofilament can also be included as an integral part of the textile fabric. That is, one or more plys of the monofilament can be included in the plys of the yarn in weaving or knitting the material. In a woven structure, such ply or plys can be included in either or both the warp or weft (fill) yarn. Subse ⁇ quent heating will soften the onofilaments to cause them to bind to the substrate material, as described above with respect to an overlaid monofilament.
  • Fig. 1 is a side view of a straight tubular vascular prosthesis in accordance with a preferred embodiment of the present invention.
  • Fig. 2 is a side view of the embodiment shown in Fig. 1 showing a bend.
  • Fig. 3 is an oblique view of a tubular vascular prosthesis in accordance with the present invention being sutured.
  • Fig. 4 is a close up view of a typical woven construction of a vascular prosthesis in accordance with an embodiment of the present invention prior to overlay ⁇ ing with a thin-line binder.
  • Fig. 5 is a close up view of the vascular prosthesis shown in Fig. 4 following overlaying with a thin-line binder.
  • Fig. 6 is a pictorial view showing a helical pattern for overlaying a thin-line binder on a vascular prosthesis in accordance with the present invention
  • Fig. 7 is a pictorial view showing a double helical pattern for overlaying a thin-line binder on a vascular prosthesis in accordance with the present invention.
  • Fig. 8 is a pictorial view showing an axial pattern for overlaying a thin-line binder on a vascular prosthesis in accordance with the present invention.
  • a tubular segment of a typical vascular prosthe ⁇ sis or graft 10 is shown.
  • Such a segment can be part of a standard long tubular stock or can be a part of a more complex structure, such as a bifurcated or branched structure.
  • a tube or tubular segment is referred to herein, it refers to any of such structures.
  • the structure is crimped typically in a spiral fashion in connection with a woven structure at crimps 12, as shown.
  • crimps 12 Although not critical to the invention, it is usual for there to be a dozen or so crimps per inch, which provides the tubular structure with the ability to be selectively elongated and bent, as required.
  • vascular prosthesis shown in Fig. 1 is illustrated in a bent configuration. Please note that the bending of prosthesis 10 does not result in kinking due to the crimping of the tubular material.
  • each of warp thread bundle 14 comprises a plurality of individual thread filaments.
  • the thread filaments are typically polyester threads, most notably polyethylene terephthalate, such as Dacron ® .
  • Other polymers have also been employed, such as Teflon ® , especially polytetrafluoroethylene.
  • weft thread bundles 16 and overlapping bundles 18 similarly bundled from a plurality of indivi ⁇ dual filaments or plys.
  • Fig. 4 is representative of structures used for vascular prostheses in general.
  • Other common structures are plain woven structures (without an overlap thread bundle) and knitted structures, which utilize a single multiple thread bundle which interlaces on itself in a locking pattern.
  • the knitted structures are not limited to one particular knit pattern, however.
  • Fig. 4 is highly magnified.
  • the mean filament diameter of a typical thread bundle used in the woven structure shown in Fig. 4 is 12-13 micrometers.
  • the spiral crimp which is shown provides a root-to-crest dimension on the order of 0.5-2.0 milli ⁇ meters for a thickness of material of 0.35 millimeters.
  • a very thin line monofilament of polypropylene 20 is laid into the root of the crimp of vascular prosthesis 10. The diameter of the monofilament is less than the root-to-crest dimension of the crimp so that to the feel there is no appreciable change in texture to the texture before the monofilament was added.
  • the monofilament is fused into the interstices of the tube by applying a controlled amount of heat to the monofilament. Such heat is obviously less than enough to melt or scorch the surface of the substrate or base material, but adequate to soften the binder. As is shown in Fig. 5, monofilament 20 fuses with all of the substrate threads it crosses, including the warp threads, the weft threads and the overlap threads wherever contact between the monofilament and these threads occurs.
  • the structure which has just been described utilizes a monofilament thin-line binder and heat for causing attachment of the thin-line binder to the overall material
  • the thin-line binder may be connected by gluing the binder to the surface.
  • gluing the binder to the surface Alter ⁇ natively to heat sealing or gluing a polypropylene monofilament in place, it is possible to provide a thin-line binder to the surface by spraying polypropylene or other suitable material in a fine jet spray to accomplish this same structure shown in Fig. 5.
  • vascular prosthesis which includes a spiral crimp prior to securing a thin-line binder to the external surface thereof.
  • knitted or woven vascular prosthesis tubes can be crimped in a circular manner rather than in a spiral manner or left uncrimped. It is not necessary to wrap each circular crimp root in order to obtain the benefits of the thin-line binder attached structure as described above. In such a construction, the alternatives illus ⁇ trated in Figs. 6, 7 and 8 are available.
  • the substrate or base tube shown in Figs. 6 and 7 are knitted tubes 22.
  • the tube is wrapped in a helical pattern with an appropriate monofilament 24 in Fig. 6 and in a double helical pattern with an appropri ⁇ ate monofilament 26 and 28 in Fig. 7.
  • Monofilament 26 is wrapped in a first direction and monofilament 28 is wrapped in the opposite direction, which may be conven ⁇ iently done by wrapping the tube with the same monofilament thread running first in one direction and then in the return direction.
  • the tube is crimped in the manner which is well known in the art for crimping such tubes. Also, such technique could be applied to tubes that are not crimped at all.
  • the location of the thin-line binder of Figs. 6 and 7 are unrelated to the location of the crimping and therefore it is expected that in some cases- the overlaid monofilament line runs up and over a crest portion of the crimp.
  • the textured surface of the overall tube is such that such a construct ⁇ ed overlaid and attached thin-line binder will not be appreciable noticed either by feel or by appearance.
  • a structure is shown wherein a monofilament line 30 is overlaid in an axial direction with respect to the vascular prosthesis tube. Additional monofilament lines 32 can be overlaid at different locations around the periphery, if desired. The overlaying may be done prior to crimping or after crimping, as desired.
  • a thread bundle used for one or more of a warp bundle, weft (fill) bundle, or overlap bundle for a woven tube or the knit bundle for a knitted tube can include one or more filaments of plys 15 of polypropylene or other suitable thin-line binder material. With the subsequent applica ⁇ tion of controlled heat, such a thin-line binder will adhere to the substrate or base material in the same fashion as described above.
  • a vascular prosthesis 10 with fraying protection provided by a thin-line binder in any of the manners previously discussed is shown in use.
  • a surgical tool 34 is shown inserting a suture near the end thereof in order to make the stitching of the vascular prosthesis in place as the surgeon desires. It is very important that the suture be located as close to the end as possible so that an excess amount of material will not be unnecessarily involved with the part of the anatomy to which the prosthesis is attached. By having the fraying and suture holding protection provided by a thin-line binder, this location can be quite near the end, as illustrated, without pulling out.
  • such thin- line binder protection makes it possible to trim the prosthesis on a bias and to handle the prosthesis extensively without causing fraying just by the manual manipulation thereof. Furthermore, its presence does not interfere with its suturability, its elongation properties, or its flexibility, only in reducing its propensity to fray, in enhancing its resistance to suture pullout and its resistance to dilation.
  • the term "stability" is used herein to refer to enhancing a tube in the manner described above to provide one or more of these enhanced properties. Because of the very thin nature of the overlaid thin-line binder with respect to the materials which are involved, the appearance and texture or feel of the overall suture is not materially changed. In addition to increasing the stability of the material, the porosity or water permeability of the material is not materially reduced by processing in any of the above manners, probably well less than 10%-15%, even with the double helical wrap shown in Fig. 7.

Abstract

On protège une prothèse vasculaire comprenant un segment en matériau tubulaire contre l'effilochage, le déchirement des bords de la suture ou sa dilatation en y incorporant un élément de liaison à filament fin fusionnant avec la surface des fibres filées ou y adhérant. Généralement, les tubes sont en polyester ou en polytétrafluoroéthylène et l'élément de liaison à filament fin est constitué d'un monofilament en polypropylène recouvert de façon appropriée avant d'être fondu ou ramolli sur place. Dans une structure à surface ondulée en spirale (10), qui s'applique à de nombreuses structures tissées ou à mailles, le monofilament (20) est déposé dans le creux de l'ondulation (12). La dimension de l'ondulation (12) depuis son creux jusqu'à sa crête dépasse l'épaisseur du monofilament (20) ou de tout autre élément de liaison à filament fin, ce qui permet d'éviter pratiquement tout changement apparent ou sensible de la structure (10) ou toute modification de la porosité. En ce qui concerne les substrats tubulaires à mailles ou autres dont la surface n'est pas ondulée en spirale, l'élément de liaison à filament fin est recouvert et fixé selon une configuration hélicoïdale, bihélicoïdale ou axiale, de préférence avant l'ondulation de la surface. La configuration à surface ondulée et la configuration de revêtement sont en l'occurence indépendantes. La stabilisation par un élément de liaison à filament fin approprié d'une structure tubulaire à surface non ondulée est également possible.
EP87902220A 1986-03-27 1987-03-10 Protheses vasculaires et procede de fabrication Withdrawn EP0261200A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US84496186A 1986-03-27 1986-03-27
US844961 1986-03-27

Publications (1)

Publication Number Publication Date
EP0261200A1 true EP0261200A1 (fr) 1988-03-30

Family

ID=25294062

Family Applications (1)

Application Number Title Priority Date Filing Date
EP87902220A Withdrawn EP0261200A1 (fr) 1986-03-27 1987-03-10 Protheses vasculaires et procede de fabrication

Country Status (9)

Country Link
EP (1) EP0261200A1 (fr)
JP (1) JPS63502886A (fr)
AU (1) AU7205487A (fr)
BR (1) BR8706774A (fr)
DK (1) DK620487A (fr)
FI (1) FI875125A (fr)
NO (1) NO874945L (fr)
PT (1) PT84548A (fr)
WO (1) WO1987005796A1 (fr)

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RU2007969C1 (ru) * 1990-03-26 1994-02-28 Виктор Владимирович Кешелава Протез для замещения трубчатых органов
US5178630A (en) * 1990-08-28 1993-01-12 Meadox Medicals, Inc. Ravel-resistant, self-supporting woven graft
DK0546021T3 (da) * 1990-08-28 1996-03-18 Meadox Medicals Inc Selvbærende vævet blodkartransplantat
SE9102448D0 (sv) * 1990-08-28 1991-08-26 Meadox Medicals Inc Ravel-resistant, self-supporting woven graft
WO1992005747A1 (fr) * 1990-10-09 1992-04-16 Moskovsky Institut Stali I Splavov Appareil destine a etre implante dans des organes creux et son dispositif d'introduction
IE71172B1 (en) * 1991-03-25 1997-01-29 Meadow Medicals Inc Vascular prosthesis
GB9116563D0 (en) * 1991-08-01 1991-09-18 Newtec Vascular Products Ltd Vascular prosthesis ii
JPH067387A (ja) * 1992-06-26 1994-01-18 Seiren Co Ltd 人工血管およびその製造方法
US5269774A (en) * 1992-09-25 1993-12-14 Gray Michael W Implantive ostomy ring
US5913894A (en) * 1994-12-05 1999-06-22 Meadox Medicals, Inc. Solid woven tubular prosthesis
US5527353A (en) 1993-12-02 1996-06-18 Meadox Medicals, Inc. Implantable tubular prosthesis
US5741332A (en) * 1995-01-23 1998-04-21 Meadox Medicals, Inc. Three-dimensional braided soft tissue prosthesis
US5641373A (en) * 1995-04-17 1997-06-24 Baxter International Inc. Method of manufacturing a radially-enlargeable PTFE tape-reinforced vascular graft
US6863686B2 (en) 1995-04-17 2005-03-08 Donald Shannon Radially expandable tape-reinforced vascular grafts
JPH11507267A (ja) * 1995-06-07 1999-06-29 バクスター・インターナショナル・インコーポレイテッド 外部から補強されたテープ強化血管移植片
US5824047A (en) * 1996-10-11 1998-10-20 C. R. Bard, Inc. Vascular graft fabric
RU2128024C1 (ru) * 1997-08-07 1999-03-27 Закрытое акционерное общество "Научно-производственный комплекс "Экофлон" Имплантируемый полый протез и способ его изготовления
US7560006B2 (en) 2001-06-11 2009-07-14 Boston Scientific Scimed, Inc. Pressure lamination method for forming composite ePTFE/textile and ePTFE/stent/textile prostheses
US20040019375A1 (en) 2002-07-26 2004-01-29 Scimed Life Systems, Inc. Sectional crimped graft
US7879085B2 (en) 2002-09-06 2011-02-01 Boston Scientific Scimed, Inc. ePTFE crimped graft
US8025693B2 (en) 2006-03-01 2011-09-27 Boston Scientific Scimed, Inc. Stent-graft having flexible geometries and methods of producing the same
PT104067B (pt) * 2008-05-21 2011-04-18 Univ Do Minho Prótese vascular em estrutura têxtil entrançada com ondulações e respectivo processo de produção
CN101856280A (zh) * 2010-06-08 2010-10-13 东华大学 一种机织人造血管及其制造方法

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Also Published As

Publication number Publication date
WO1987005796A1 (fr) 1987-10-08
DK620487D0 (da) 1987-11-26
BR8706774A (pt) 1988-02-23
NO874945D0 (no) 1987-11-26
JPS63502886A (ja) 1988-10-27
DK620487A (da) 1987-11-26
FI875125A0 (fi) 1987-11-19
PT84548A (en) 1987-04-01
AU7205487A (en) 1987-10-20
FI875125A (fi) 1987-11-19
NO874945L (no) 1987-11-26

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