CA1143105A - Tubular organic prosthesis and process for production thereof - Google Patents

Tubular organic prosthesis and process for production thereof

Info

Publication number
CA1143105A
CA1143105A CA000337440A CA337440A CA1143105A CA 1143105 A CA1143105 A CA 1143105A CA 000337440 A CA000337440 A CA 000337440A CA 337440 A CA337440 A CA 337440A CA 1143105 A CA1143105 A CA 1143105A
Authority
CA
Canada
Prior art keywords
prosthesis
fibers
tubing
polyurethane
elastic fibers
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.)
Expired
Application number
CA000337440A
Other languages
French (fr)
Inventor
Hiroshi Mano
Toshisaburo Oga
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.)
Sumitomo Electric Industries Ltd
Original Assignee
Sumitomo Electric Industries 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
Application filed by Sumitomo Electric Industries Ltd filed Critical Sumitomo Electric Industries Ltd
Application granted granted Critical
Publication of CA1143105A publication Critical patent/CA1143105A/en
Expired 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
    • A61L27/14—Macromolecular materials
    • A61L27/16—Macromolecular materials obtained by reactions only involving carbon-to-carbon unsaturated bonds

Abstract

S-2-22319C/79 A tubular organic prosthesis comprising a porous tubing ofpolytetrafluoroethylene and elastic fibers provided helically on its outside surface, and a process for preparing the same is disclosed.

Description

S
BACKGROUND OF THE INVENTION
, .
1. Field of the Invention , _ .
This invention relates to an improvement in and relating to a tubular organic prosthesis composed of a porous tubing of polytetrafluoroethylene (abbreviated "PTFE" ), and is directed to increasing the strength of the tubing and its ability to connect with the tissues of a patient.
2. Description of the Prior Art -Many reports have been made heretofore to sho~ that a porous tubing o~ PTFE produced by a stretching method can be clinically used as a tubular organic prosthesis, especially as a vascular prosthesis. Such a prosthesis îs regarded as better than conventional prostheses made of knitted or woven fabrics. A PTFE
tubing ~hich has been su~jected to a stretching -treatment has a microstructure composed of very fine fibers and nodes connected to one another by the fibers. The diameters of the fibers vary depending on stretching conditions, and can be made muc~ smaller than those of the fibers of the knitted or woven fabrics mentioned above. Moreover, since the pore diameter and porosity of the tubing can be varied freely, when it is used, for example, as an artificial vessel, it is pliable and scarcely permits formation of thrombus. The tubing also shows good formation of a pseudointima on the inner surface without any appreciable adverse effect on the surrounding tissues. Thus, the stretched tubing is regarded as one of the best prostheses for tubular organs.
The stretched PTFE tubing, however, has the disadvantage that when it is used as a tubular organic prosthesis and joined with the living body, the needle or suture tends to tear the tubing. This tearing frequently occurs in the axial direction of the porous PTFE tubing. Since this is due to the orientation of ?~-~
3~5 1 the fine PTFE fibers formed as a result of stretching, it can be reduced to some extent by biaxially stretching the tu~ing, namely stretching it in the axial direction and expanding its diameter, there~y to change the structure of the fine fibers to a radial orientation. A great improvement in strength, however, cannot be expected from this process alone. Furthermore, it is difficult for natural occlusion of suture holes to occur based on the elasticity of the porous PTFE tu~ing alone, and when it is used as an artificial vessel, bleeding from the suture holes is also a problem. Further, when it is sharply bent it buckles and cannot retain a cylindrical shape. This is also a drawback in practical application.
The present invention offers a solution to these problems in a junction operation.
SUMMARY OF THE INVENTION
.. . . . . _ It is an object of this invention to provide a tubular organic prosthesis comprising a porous PTFE tubing and elastic fibers provided helically on its outside surface.

Another object of this invention is to provide a tubular organic prosthesis which permits easy entry and attachment of the surrounding tissues to promote the assimilation of the prosthesis.
According to this invention, there is provided a tuhular organic prosthesis comprising a porous tubing of polytetrafluoro-ethylene and elastic fibers provided helically on its outside surface.
In another aspect, the invention provides a process for producing a tubular organic prosthesis which comprises wrapping elastic fibers helically about the outside surface of a porous tubing of polytetrafluoroethylene, impregnating the resulting ~3~
1 structure with a solvent c~pable of dissolving or swelling the elastic fibers to thereby ~ond them to the PTFE tubing, drying the structure, and then heat-setting.

DETAILED DESCRIPTION OF THE INVENTION
As a result of providing elastic fibers helically on the outside surface of the porous PTFE tubing, the porous PTFE
tubing of the present invention does not undergo tearing by a joining needle or suture. It also has the advantage that when the tubing together with the elastic fibers is sutured at the time of a junction operation, the holes left after joining are occluded by the elasticity of the fibers. Furthermore, since the elastic fibers are helically oriented, the tubing is pliable in the longitudinal direction, and even when it is sharply hent, it does not easily buckle. In addition, spaces for easy entry of the surrounding tissues of a patient are available on the outside surface of the tubing and this accelerate the assimilation of the porous PTFE tubing as an organic prosthesis.
The porous tubing of PTFE in accodance with this invention is produced by the method described in Japanese Patent Publication No. 13560~67 and~ e.g., U.S. Patents 3,953,566 and 3,962,153.
liquid lubricant is mixed with an unsintered powder of poly-tetrafluoroethylene and the mixture is extruded into a tubular form by a ram-type extruder. The PTFE used in this invention preferably has a molecular weight of 106 to 107. The tubing is stretched at least monoaxially after the liquid lubricant is optionally removed. Preferably, the tubing is stretched in the axial direction, and its diameter is expanded~ The tubing is heated at a temperature above 327C which is the sintering temperature while fixing it in place to avoid shrinkage. Thus, the stretched and expanded structure is fixed and a tubing having increased strength is obtained. The resulting porous PTFE tubing ~3~(~5 has a microstructure composed of very fine fibers and nodes connected to one another by these fibers. Because the diameters and lengths oE these fibers and the sizes and number o~ the nodes can be varied depending upon the stretching and sintering conditions, the pore diameter and porosity of the resulting porous tubing can be determined freely. It has been clinically confirmed that when this tubing is used as a vascular prosthesis, it suitabl~ has an average pore diameter of about 2f~m to aboutlOO~lm, a porosity of at least about 70~, and a wall thickness of about 0.3 to 1.0 mm.
In the microstructure of the porous PTFE tubing preferred in this invention, the fibers are distributed not unidirectionally but radially. This fibrous structure is obtained by biaxially stretching the PTFE tubing, namely by stretching it in the axial direction and expanding its diameter. Expansion of its diameter can be achieved by reducing the pressure on the outside surface of the t~bing, or pressing its inside surface, or simultaneously preforming these two procedures, while heating. Alternatively, the diameter of the tubing may be mechanically enlarged by passing an article of a suita~le configuration through the inside of the tubing. Stretching of the tubing in the axial direction and expansion of its diameter are carried out simultaneously or successively, or may be carried out simultaneously with the final sintering step. The porous PTFE tubing obtained by the biaxial stretching method is more pliable and less prone to longitudinal tearing than a porous PTFE tubing stretched only in the axial direction because the fibers are distributed not only in the axial direction but radially in all directions. However, to perform a junction operation using this biaxially stretched porous PTFE

tubing, more improvements in strength, natural occlusion of the suture holes, bending property, and the ability to connect with the tissues of a patient are desired.

,.

~3~35 1 In accordance wi~h th;s invention elastic fibers are helically provided on the outside surface of the porous PTFE
tubing to solve the aforesaid problems.
The elastic fihers are fihers produced from at least 50~ elastomer. They include polyurethane fibers and fibers from various rubbers (so-called rubber yarns), e.g., silicone rubbers, fluorine rubhers, acrylic rubbers, natural rubber, etc. Examples of non-elastomers which may be present in combination with the ela~tomers include polyamides, polyesters, polypropylenes, etc.
The elastîc fibers used in this invention are described in detail below with re~erence to polyurethane fibers which constitute a preferred embodiment of the present invention. Substantially the same description will apply to other elastic fibers.
Preferably fibers are selected and wrapped around the prosthesis to give it a suture tear resistance of at least 300 g/ply.
The polyurethane elastic fibers are made from an orgainic diis-icyanate and a polyether or polyester and are characterized by their elasticity. Polyurethane fibers normally used for apparel are also suitable for the purpose of this invention. Polyurethane elastic fibers of the polyether type are sepecially suitable for organic prostheses.
The fibers may be in the form of monofilaments or multifilaments. Not only bare yarns of polyurethane but also processed or modified yarns can be used to achieve the objects of this invention. Commerically available processed yarns include covered yarns having other fibers wrapped thereabout, core spun yar~s having polyurethane fibers as a core, ply yarns, etc. All of these yarns can be used in this invention. The polyurethane elastic yarns usually have a tensile strength of about l to 1.5 g/denier (ASTM D-63g) and those having a size of about 150 denier L L~L 310 S

1 to a~out 5,000 denier are effective.
To provide the elastic fi~ers helically on the outside surface of the porous PTFE tubing, the fibers are first helically wrapped about the outside surface of t:he tubing. The fi~ers may be wrapped in close contact with one another, or at some interval, preferably not exceeding the diameter of the prosthesis.
A suita~lc thickness of the fiber wrapping ranges from a~out 0.05 mm to about l mm.
~ fter wrapping, the fibers are impregnated with a 10- solvent capable of dissolving or swelling the elastic fibers to dissolve the elastic fibers partly and bond them to the PTFE tubing.
Suitable solvents for the polyure~hane elastic fi~ers include phenol, m-cresol, benzene, toluene, formic acid, tetrahydrofuran, N,N-dimethylformamide and N,N-dimethylacetamide. The structure impregnated with the solvent is dried, and then heated at a suitable temperature to heat-set it. This heat-setting relaxes the residual stress of the helically wrapped elastic fi~ers, and sets their configuration. The heat-setting temperature and time are determined according to the material of the elastic fibers.
In the case of polyurethane elastic fibers, heat-setting is usually carried out at a temperature of about 120 to 230C for a period of l to 60 minutes. Heating may be effected in air or with steam or the like.
The tubular organic prosthesis of this invention descri~ed hereinabove is very useful as an artificial vessel, ~ut can also ~e used for the prosthesis of other tubular organs including the esophagus, trachea, biliary duct, ureter, and urethra.
The following Examples illustrated the present invention more specifically. It should be understood that the scope of the invention is not limited by these Examples.

:B.1~3105 1 EX~MPLE 1 One hundred parts by weight of fine PTFE powder, Polyflon F-104 (a trademark for a product of Daikin Kogyo Co., Ltd.,) was mixed uniformly with 29 parts by weight of a liquid lubricant (Deobase). The mixture was pre-formed under pressure and extruded by a ram-type extruder into a tubing having an inside diameter of 3.0 mm and an outside diameter of 4.5 mm. The tubing was dipped in trichloroethylene to extract and remove the liquid lubricant, and then stretched 200% in the axial direction of thP
1~ tubing while it was heated at about 250C. The stretched tubing was then heated at 350C while reducing the pressure on the outside surface of the tubing to expand its diameter and simulta~eously sinter the tubing. The tubing obtained was a porous tubing having an inside diameter of 4.0 mm, and outside diameter of 4.9 mm, and a porosity of 79~.
A stainless steel rod having a diameter of 4.0 mm was inserted in the porous PTFE tubing, and elastic polyurethane multifilaments having a size of 1,120 denier were densely wrapped helically about the outside surface of the tubing. The filaments were fixed at both ends, and impregnated with tetrahydrofuran to bond them. The resulting strwcture was dried and heated at 170C
for 10 minutes to heat-set the fibers. The resulting tubing did not deform even when the stainless steel rod was withdrawn. It was pliable and hadhigh flexibility. When a stainless steel wire having a diameter of 0.40 mm was inserted in a loop-like config-uration into the wall of the tubing at 5 mm from one end of the tubing, and pulled in the axial direction of the tubing at a speed of 50 mm/min., tearing occurred in the tubing under a load of 1,250 g which is much larger than the load (180 g) under which tearing occurred in the tubing without the elastic fibers. Holes ~3~5 1 left a~ter inserting a surgical suturing needle were naturally occluded by the elasticity of the elastic fibers. Thus, the resulting product had various superior characteristics as a tubular organic prosthesis.
EX~MPLE 2 .
Elastic polyurethane multifilamen~s having a slze of 2,240 denier were wrapped helicall~ at invervals of 0.5 mm about the outside surface of the same porous PTFE tubing as used in Example 1, and treated in the same way as in Example 1. The load under w~ich teariny occurred in the resulting tubing was 860 g.
Thus, the product had superior characteristics as a tu~ular organic prosthesis as in the case of the tu~ing obtained in Example 1.
While the invention has been described in detail and with reference to specific embodiments thereof, it will be apparent to one skilled in the art that various changes and modifications can be made therein without departing from the spirit and scope thereof.

~0

Claims (17)

The embodiments of the invention in which an exclusive property or privilege is claimed are defined as follows:
1. A tubular organic prosthesis comprising a porous tubing of polytetrafluoroethylene and elastic fibers provided helically on its outside surface.
2. The prosthesis of Claim 1, wherein said polytetrafluoro-ethylene tubing has a microstructure composed of fibers and nodes connected to one another by said fibers, said fibers being radially distributed.
3. The prosthesis of Claim 1, wherein said elastic fibers are made from polyurethane.
4. The prosthesis of Claim 1, wherein said elastic fibers are rubber yarns.
5. The prosthesis of Claim 1, wherein said fibers have a denier of about 150 to about 5,000.
6. The prosthesis of Claim 1, wherein said fibers have a tensile strength of about 1 g/denier.
7. The prosthesis of Claim 1, wherein said PTFE tubing has a porosity of at least about 70%.
8. The prosthesis of Claim 1, wherein said PTFE tubing has a wall thickness of about 0.3 to 1.0 mm.
9. The prosthesis of Claim 1, wherein said PTFE tubing has an average pore diameter of about 2µm to about 100µm.
10. The prosthesis of Claim 3, wherein said polyurethane is a polyether polyurethane.
11. The prosthesis of Claim 1, wherein said prosthesis has a suture tear resistance of about 300 g/ply or more.
12. A process for producing a tubular organic prosthesis, which comprises wrapping elastic fibers helically about the outside surface of a porous tubing of polytetrafluoroethylene, impregnating the resulting structure with a solvent capable of dissolving or swelling said elastic fibers thereby to bond them, drying the structure, and then heat-setting the fibers.
13. The process of Claim 12, wherein said elastic fibers are made from a polyurethane.
14. The process of Claim 12, wherein said polyurethane is a polyether polyurethane.
15. The process of Claim 12, wherein said heat-setting is conducted at a temperature of about 120 to 230°C over a period of about 1 to 60 minutes.
16. The process of Claim 12, wherein said solvent is selected from the group consisting of phenol, m-cresol, benzene, toluene, formic acid, tetrahydrofuran, N,N-dimethylformamide and N,N-dimethylacetamide.
17. The process of Claim 12, wherein said fibers have a size of about 150 to about 5,000 denier.
CA000337440A 1978-10-12 1979-10-12 Tubular organic prosthesis and process for production thereof Expired CA1143105A (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP125953/78 1978-10-12
JP53125953A JPS6037734B2 (en) 1978-10-12 1978-10-12 Tubular organ prosthesis material and its manufacturing method

Publications (1)

Publication Number Publication Date
CA1143105A true CA1143105A (en) 1983-03-22

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Family Applications (1)

Application Number Title Priority Date Filing Date
CA000337440A Expired CA1143105A (en) 1978-10-12 1979-10-12 Tubular organic prosthesis and process for production thereof

Country Status (11)

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US (2) US4306318A (en)
JP (1) JPS6037734B2 (en)
AU (1) AU527117B2 (en)
BE (1) BE879355A (en)
CA (1) CA1143105A (en)
DE (1) DE2941279A1 (en)
FR (1) FR2438472A1 (en)
GB (1) GB2033233B (en)
IT (1) IT1164833B (en)
NL (1) NL173135C (en)
SE (1) SE7908447L (en)

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NL173135B (en) 1983-07-18
FR2438472B1 (en) 1984-11-30
JPS5552755A (en) 1980-04-17
JPS6037734B2 (en) 1985-08-28
IT7950512A0 (en) 1979-10-10
GB2033233A (en) 1980-05-21
AU5169379A (en) 1980-04-17
BE879355A (en) 1980-02-01
NL7907531A (en) 1980-04-15
DE2941279A1 (en) 1980-04-17
IT1164833B (en) 1987-04-15
SE7908447L (en) 1980-04-13
US4306318A (en) 1981-12-22
AU527117B2 (en) 1983-02-17
FR2438472A1 (en) 1980-05-09
GB2033233B (en) 1983-05-11
NL173135C (en) 1983-12-16
USRE31618E (en) 1984-07-03

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