USRE31618E - Tubular organic prosthesis - Google Patents
Tubular organic prosthesis Download PDFInfo
- Publication number
- USRE31618E USRE31618E US06/369,962 US36996282A USRE31618E US RE31618 E USRE31618 E US RE31618E US 36996282 A US36996282 A US 36996282A US RE31618 E USRE31618 E US RE31618E
- Authority
- US
- United States
- Prior art keywords
- prosthesis
- tubing
- fibers
- elastic fibers
- polyurethane
- 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 - Lifetime
Links
- 229920001343 polytetrafluoroethylene Polymers 0.000 claims abstract description 37
- 239000004810 polytetrafluoroethylene Substances 0.000 claims abstract description 37
- 210000004177 elastic tissue Anatomy 0.000 claims abstract description 27
- -1 polytetrafluoroethylene Polymers 0.000 claims abstract description 8
- 239000000835 fiber Substances 0.000 claims description 27
- 229920002635 polyurethane Polymers 0.000 claims description 11
- 239000004814 polyurethane Substances 0.000 claims description 11
- 229920001971 elastomer Polymers 0.000 claims description 7
- 239000011148 porous material Substances 0.000 claims description 4
- 239000005060 rubber Substances 0.000 claims description 4
- 239000004721 Polyphenylene oxide Substances 0.000 claims description 3
- 229920000570 polyether Polymers 0.000 claims description 3
- 230000002792 vascular Effects 0.000 claims description 3
- 238000000034 method Methods 0.000 description 6
- 210000001519 tissue Anatomy 0.000 description 5
- WYURNTSHIVDZCO-UHFFFAOYSA-N Tetrahydrofuran Chemical compound C1CCOC1 WYURNTSHIVDZCO-UHFFFAOYSA-N 0.000 description 4
- 238000009998 heat setting Methods 0.000 description 4
- 239000010687 lubricating oil Substances 0.000 description 4
- 229920006306 polyurethane fiber Polymers 0.000 description 4
- 239000002904 solvent Substances 0.000 description 4
- UHOVQNZJYSORNB-UHFFFAOYSA-N Benzene Chemical compound C1=CC=CC=C1 UHOVQNZJYSORNB-UHFFFAOYSA-N 0.000 description 3
- ZMXDDKWLCZADIW-UHFFFAOYSA-N N,N-Dimethylformamide Chemical compound CN(C)C=O ZMXDDKWLCZADIW-UHFFFAOYSA-N 0.000 description 3
- YXFVVABEGXRONW-UHFFFAOYSA-N Toluene Chemical compound CC1=CC=CC=C1 YXFVVABEGXRONW-UHFFFAOYSA-N 0.000 description 3
- 239000000806 elastomer Substances 0.000 description 3
- 230000006872 improvement Effects 0.000 description 3
- 238000005245 sintering Methods 0.000 description 3
- 229910001220 stainless steel Inorganic materials 0.000 description 3
- ISWSIDIOOBJBQZ-UHFFFAOYSA-N Phenol Chemical compound OC1=CC=CC=C1 ISWSIDIOOBJBQZ-UHFFFAOYSA-N 0.000 description 2
- 230000015572 biosynthetic process Effects 0.000 description 2
- 238000010438 heat treatment Methods 0.000 description 2
- RLSSMJSEOOYNOY-UHFFFAOYSA-N m-cresol Chemical compound CC1=CC=CC(O)=C1 RLSSMJSEOOYNOY-UHFFFAOYSA-N 0.000 description 2
- BDAGIHXWWSANSR-UHFFFAOYSA-N methanoic acid Natural products OC=O BDAGIHXWWSANSR-UHFFFAOYSA-N 0.000 description 2
- 239000000203 mixture Substances 0.000 description 2
- 210000000056 organ Anatomy 0.000 description 2
- 229920000728 polyester Polymers 0.000 description 2
- 239000000843 powder Substances 0.000 description 2
- 230000008569 process Effects 0.000 description 2
- 239000010935 stainless steel Substances 0.000 description 2
- 230000008961 swelling Effects 0.000 description 2
- YLQBMQCUIZJEEH-UHFFFAOYSA-N tetrahydrofuran Natural products C=1C=COC=1 YLQBMQCUIZJEEH-UHFFFAOYSA-N 0.000 description 2
- 239000002759 woven fabric Substances 0.000 description 2
- OSWFIVFLDKOXQC-UHFFFAOYSA-N 4-(3-methoxyphenyl)aniline Chemical compound COC1=CC=CC(C=2C=CC(N)=CC=2)=C1 OSWFIVFLDKOXQC-UHFFFAOYSA-N 0.000 description 1
- YCKRFDGAMUMZLT-UHFFFAOYSA-N Fluorine atom Chemical compound [F] YCKRFDGAMUMZLT-UHFFFAOYSA-N 0.000 description 1
- 244000043261 Hevea brasiliensis Species 0.000 description 1
- FXHOOIRPVKKKFG-UHFFFAOYSA-N N,N-Dimethylacetamide Chemical compound CN(C)C(C)=O FXHOOIRPVKKKFG-UHFFFAOYSA-N 0.000 description 1
- 239000004952 Polyamide Substances 0.000 description 1
- 229920006361 Polyflon Polymers 0.000 description 1
- 239000004743 Polypropylene Substances 0.000 description 1
- 208000007536 Thrombosis Diseases 0.000 description 1
- XSTXAVWGXDQKEL-UHFFFAOYSA-N Trichloroethylene Chemical group ClC=C(Cl)Cl XSTXAVWGXDQKEL-UHFFFAOYSA-N 0.000 description 1
- 229920000800 acrylic rubber Polymers 0.000 description 1
- 230000002411 adverse Effects 0.000 description 1
- 238000005452 bending Methods 0.000 description 1
- 230000008901 benefit Effects 0.000 description 1
- 230000000740 bleeding effect Effects 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 125000005442 diisocyanate group Chemical group 0.000 description 1
- 238000001035 drying Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 210000003238 esophagus Anatomy 0.000 description 1
- 229910052731 fluorine Inorganic materials 0.000 description 1
- 239000011737 fluorine Substances 0.000 description 1
- 235000019253 formic acid Nutrition 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 229920003052 natural elastomer Polymers 0.000 description 1
- 229920001194 natural rubber Polymers 0.000 description 1
- 229920000058 polyacrylate Polymers 0.000 description 1
- 229920002647 polyamide Polymers 0.000 description 1
- 229920001155 polypropylene Polymers 0.000 description 1
- 229920002379 silicone rubber Polymers 0.000 description 1
- 210000003437 trachea Anatomy 0.000 description 1
- UBOXGVDOUJQMTN-UHFFFAOYSA-N trichloroethylene Natural products ClCC(Cl)Cl UBOXGVDOUJQMTN-UHFFFAOYSA-N 0.000 description 1
- 210000000626 ureter Anatomy 0.000 description 1
- 210000003708 urethra Anatomy 0.000 description 1
Images
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
Definitions
- 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.
- PTFE polytetrafluoroethylene
- a porous tubing of PTFE produced by a stretching method can be clinically used as a tubular organic prosthesis, especially as a vascular prosthesis.
- Such a prosthesis is regarded as better than conventional prostheses made of knitted or woven fabrics.
- a PTFE tubing which has been subjected 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 much smaller than those of the fibers of the knitted or woven fabrics mentioned above.
- the pore diameter and porosity of the tubing can be varied freely, when it is used, for example, as an artifical 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.
- the stretched tubing is regarded as one of the best prostheses for tubular organs.
- the stretched PTFE tubing 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 the fine PTFE fibers formed as a result of stretching, it can be reduced to some extent by biaxially stretching the tubing, namely stretching it in the axial direction and expanding its diameter, thereby 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.
- the present invention offers a solution to these problems in a junction operation.
- 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.
- a tubular organic prosthesis comprising a porous tubing of polytetrafluoroethylene and elastic fibers provided helically on its outside surface.
- 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 structure with a solvent capable of dissolving or swelling the elastic fibers to thereby bond them to the PTFE tubing, drying the structure, and then heat-setting.
- the FIGURE is a side view of the tubular prosthesis showing the essential elements thereof.
- Said tubular prosthesis is provided with a body of porous PTFE 1, which body is helically provided with elastic fibers upon its outer surface 2.
- 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 bent, 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 accordance with this invention is produced by the method described in Japanese Patent Publication No. 13560/67 and, e.g., U.S. Pat. Nos. 3,953,566 and 3,962,153.
- a liquid lubricant is mixed with an unsintered powder of polytetrafluoroethylene 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 10 6 to 10 7 .
- the tubing is stretched at least monoaxially after the liquid lubricant is optionally removed.
- the tubing is stretched in the axial direction, and its diameter is expanded.
- the tubing is heated at a temperature above 327° C.
- the resulting porous PTFE tubing has a microstructure composed of very fine fibers and nodes connected to one another by these fibers. Because the diameters and lengths of these fibers and the sizes and number of 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.
- this tubing when used as a vascular prosthesis, it suitably has an average pore diameter of about 2 ⁇ m to about 100 ⁇ m, a porosity of at least about 70%, and a wall thickness of about 0.3 to 1.0 mm.
- 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 tubing, or pressing its inside surface, or simultaneously performing these two procedures, while heating. Alternatively, the diameter of the tubing may be mechanically enlarged by passing an article of a suitable 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.
- 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.
- elastic fibers are helically provided on the outside surface of the porous PTFE tubing to solve the aforesaid problems.
- the elastic fibers are fibers produced from at least 50% elastomer. They include polyurethane fibers and fibers from various rubbers (so-called rubber yarns), e.g., silicone rubbers, fluorine rubbers, acrylic rubbers, natural rubber, etc. Examples of non-elastomers which may be present in combination with the elastomers include polyamides, polyesters, polypropylenes, etc.
- the elastic fibers used in this invention are described in detail below with reference 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 organic diisocyanate and a polyether or polyester and are characterized by their elasticity. Polyurethane fibers normally used for apparel are also suitable for the purposes of this invention. Polyurethane elastic fibers of the polyether type are especially 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.
- Commercally available processed yarns include covered yarns having other fibers wrapped thereabout, core spun yarns 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 1 to 1.5 g/denier (ASTM D-638) and those having a size of about 150 denier to about 5,000 denier are effective.
- the fibers are first helically wrapped about the outside surface of the tubing.
- the fibers may be wrapped in close contact with one another, or at some interval, preferably not exceeding the diameter of the prosthesis.
- a suitable thickness of the fiber wrapping ranges from about 0.05 mm to about 1 mm.
- the fibers are impregnated with a 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 polyurethane elastic fibers 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 fibers, 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 230° C. for a period of 1 to 60 minutes. Heating may be effected in air or with steam or the like.
- tubular organic prosthesis of this invention is very useful as an artificial vessel, but can also be used for the prosthesis of other tubular organs including the esophagus, trachea, biliary duct, ureter, and urethra.
- 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 the tubing while it was heated at about 250° C. The stretched tubing was then heated at 350° C.
- 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 structure was dried and heated at 170° C. 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 had high flexibility.
- Elastic polyurethane multifilaments having a size of 2,240 denier were wrapped helically at intervals 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 which tearing occurred in the resulting tubing was 860 g.
- the product had superior characteristics as a tubular organic prosthesis as in the case of the tubing obtained in Example 1.
Abstract
A tubular organic prosthesis comprising a porous tubing of polytetrafluoroethylene and elastic fibers provided helically on its outside surface.
Description
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 show that a porous tubing of PTFE produced by a stretching method can be clinically used as a tubular organic prosthesis, especially as a vascular prosthesis. Such a prosthesis is regarded as better than conventional prostheses made of knitted or woven fabrics. A PTFE tubing which has been subjected 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 much 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 artifical 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 the fine PTFE fibers formed as a result of stretching, it can be reduced to some extent by biaxially stretching the tubing, namely stretching it in the axial direction and expanding its diameter, thereby 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 tubing 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.
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 tubular organic prosthesis comprising a porous tubing of polytetrafluoroethylene 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 structure with a solvent capable of dissolving or swelling the elastic fibers to thereby bond them to the PTFE tubing, drying the structure, and then heat-setting.
The FIGURE is a side view of the tubular prosthesis showing the essential elements thereof. Said tubular prosthesis is provided with a body of porous PTFE 1, which body is helically provided with elastic fibers upon its outer surface 2.
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 bent, 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 accordance with this invention is produced by the method described in Japanese Patent Publication No. 13560/67 and, e.g., U.S. Pat. Nos. 3,953,566 and 3,962,153. A liquid lubricant is mixed with an unsintered powder of polytetrafluoroethylene 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 327° C. 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 has a microstructure composed of very fine fibers and nodes connected to one another by these fibers. Because the diameters and lengths of these fibers and the sizes and number of 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 suitably has an average pore diameter of about 2 μm to about 100 μm, 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 tubing, or pressing its inside surface, or simultaneously performing these two procedures, while heating. Alternatively, the diameter of the tubing may be mechanically enlarged by passing an article of a suitable 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.
In accordance with this invention elastic fibers are helically provided on the outside surface of the porous PTFE tubing to solve the aforesaid problems.
The elastic fibers are fibers produced from at least 50% elastomer. They include polyurethane fibers and fibers from various rubbers (so-called rubber yarns), e.g., silicone rubbers, fluorine rubbers, acrylic rubbers, natural rubber, etc. Examples of non-elastomers which may be present in combination with the elastomers include polyamides, polyesters, polypropylenes, etc. The elastic fibers used in this invention are described in detail below with reference 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 organic diisocyanate and a polyether or polyester and are characterized by their elasticity. Polyurethane fibers normally used for apparel are also suitable for the purposes of this invention. Polyurethane elastic fibers of the polyether type are especially 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. Commercally available processed yarns include covered yarns having other fibers wrapped thereabout, core spun yarns 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 1 to 1.5 g/denier (ASTM D-638) and those having a size of about 150 denier to about 5,000 denier are effective.
To provide the elastic fibers helically on the outside surface of the porous PTFE tubing, the fibers are first helically wrapped about the outside surface of the tubing. The fibers may be wrapped in close contact with one another, or at some interval, preferably not exceeding the diameter of the prosthesis. A suitable thickness of the fiber wrapping ranges from about 0.05 mm to about 1 mm.
After wrapping, the fibers are impregnated with a 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 polyurethane elastic fibers 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 fibers, 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 230° C. for a period of 1 to 60 minutes. Heating may be effected in air or with steam or the like.
The tubular organic prosthesis of this invention described hereinabove is very useful as an artificial vessel, but can also be used for the prosthesis of other tubular organs including the esophagus, trachea, biliary duct, ureter, and urethra.
The following Examples illustrate the present invention more specifically. It should be understood that the scope of the invention is not limited by these Examples.
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 the tubing while it was heated at about 250° C. The stretched tubing was then heated at 350° C. while reducing the pressure on the outside surface of the tubing to expand its diameter and simultaneously 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 structure was dried and heated at 170° C. 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 had high flexibility. When a stainless steel wire having a diameter of 0.40 mm was inserted in a loop-like configuration 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 left after 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.
Elastic polyurethane multifilaments having a size of 2,240 denier were wrapped helically at intervals 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 which tearing occurred in the resulting tubing was 860 g. Thus, the product had superior characteristics as a tubular organic prosthesis as in the case of the tubing 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.
Claims (14)
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 polytetrafluoroethylene 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 3, wherein said polyurethane is a polyether polyurethane.
5. The prosthesis of claim 4, wherein said prosthesis has a suture tear resistance of about 300 g/ply or more.
6. The prosthesis of claim 1, wherein said elastic fibers are rubber yarns.
7. The prosthesis of claim 1, wherein said fibers have a denier of about 150 to about 5,000.
8. The prosthesis of claim 1, wherein said fibers have a tensile strength of about 1 g/denier.
9. The prosthesis of claim 1, wherein said PTFE tubing has a porosity of at least about 70%.
10. The prosthesis of claim 1, wherein said PTFE tubing has a wall thickness of about 0.3 to 1.0 mm.
11. The prosthesis of claim 1, wherein said PTFE tubing has an average pore diameter of about 2 μm to about 100 μm.
12. The prosthesis of claim 1, wherein said prosthesis has a suture tear resistance of about 300 g/ply or more.
13. The tubular organic prosthesis of claim 1, wherein said tubular organic prosthesis is a vascular prosthesis.
14. The prosthesis of claim 13, wherein said prosthesis has a suture tear resistance of about 300 g/ply or more.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP53-125953 | 1978-10-12 | ||
JP53125953A JPS6037734B2 (en) | 1978-10-12 | 1978-10-12 | Tubular organ prosthesis material and its manufacturing method |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US06/084,325 Reissue US4306318A (en) | 1978-10-12 | 1979-10-12 | Tubular organic prosthesis |
Publications (1)
Publication Number | Publication Date |
---|---|
USRE31618E true USRE31618E (en) | 1984-07-03 |
Family
ID=14923052
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US06/084,325 Ceased US4306318A (en) | 1978-10-12 | 1979-10-12 | Tubular organic prosthesis |
US06/369,962 Expired - Lifetime USRE31618E (en) | 1978-10-12 | 1982-04-19 | Tubular organic prosthesis |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US06/084,325 Ceased US4306318A (en) | 1978-10-12 | 1979-10-12 | Tubular organic prosthesis |
Country Status (11)
Country | Link |
---|---|
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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Also Published As
Publication number | Publication date |
---|---|
JPS6037734B2 (en) | 1985-08-28 |
IT1164833B (en) | 1987-04-15 |
NL173135B (en) | 1983-07-18 |
FR2438472B1 (en) | 1984-11-30 |
NL7907531A (en) | 1980-04-15 |
SE7908447L (en) | 1980-04-13 |
JPS5552755A (en) | 1980-04-17 |
US4306318A (en) | 1981-12-22 |
GB2033233B (en) | 1983-05-11 |
IT7950512A0 (en) | 1979-10-10 |
AU5169379A (en) | 1980-04-17 |
NL173135C (en) | 1983-12-16 |
BE879355A (en) | 1980-02-01 |
DE2941279A1 (en) | 1980-04-17 |
GB2033233A (en) | 1980-05-21 |
CA1143105A (en) | 1983-03-22 |
FR2438472A1 (en) | 1980-05-09 |
AU527117B2 (en) | 1983-02-17 |
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