CA1143105A - Tubular organic prosthesis and process for production thereof - Google Patents
Tubular organic prosthesis and process for production thereofInfo
- 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
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.
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 ?~-~
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
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)
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.
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 |
Family
ID=14923052
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)
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) |
Families Citing this family (161)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE2932435A1 (en) * | 1979-08-10 | 1981-02-26 | Bayer Ag | IMPLANT FOR BIOLOGICAL BODY PARTS, IN PARTICULAR DENTAL IMPLANT FOR THE JAW |
DE3019996A1 (en) * | 1980-05-24 | 1981-12-03 | Institute für Textil- und Faserforschung Stuttgart, 7410 Reutlingen | HOHLORGAN |
US4604762A (en) * | 1981-02-13 | 1986-08-12 | Thoratec Laboratories Corporation | Arterial graft prosthesis |
DE3478192D1 (en) * | 1983-06-06 | 1989-06-22 | Kanegafuchi Chemical Ind | Artificial vessel and process for preparing the same |
EP0128501B1 (en) * | 1983-06-06 | 1989-03-29 | Kanegafuchi Kagaku Kogyo Kabushiki Kaisha | Artificial vessel and process for preparing the same |
US4647416A (en) * | 1983-08-03 | 1987-03-03 | Shiley Incorporated | Method of preparing a vascular graft prosthesis |
US4550447A (en) * | 1983-08-03 | 1985-11-05 | Shiley Incorporated | Vascular graft prosthesis |
DE3345513A1 (en) * | 1983-12-16 | 1985-07-04 | B. Braun Melsungen Ag, 3508 Melsungen | METHOD FOR PRODUCING A VESSEL PROSTHESIS |
EP0157178B1 (en) * | 1984-03-01 | 1988-11-30 | Kanegafuchi Kagaku Kogyo Kabushiki Kaisha | Artificial vessel and process for preparing the same |
US4573471A (en) * | 1984-07-09 | 1986-03-04 | Rudner Merritt A | Prosthetic apparatus for surgical anastomosis |
JPS6156659A (en) * | 1984-08-13 | 1986-03-22 | エヌオーケー株式会社 | Immobilization of biologically active substance |
JPS6168038A (en) * | 1984-09-10 | 1986-04-08 | 住友ベークライト株式会社 | Artificial trachea |
SE450809B (en) * | 1985-04-10 | 1987-08-03 | Medinvent Sa | PLANT TOPIC PROVIDED FOR MANUFACTURING A SPIRAL SPRING SUITABLE FOR TRANSLUMINAL IMPLANTATION AND MANUFACTURED SPIRAL SPRINGS |
JPH0669488B2 (en) * | 1985-05-23 | 1994-09-07 | 呉羽化学工業株式会社 | Transdermal composite |
US4652263A (en) * | 1985-06-20 | 1987-03-24 | Atrium Medical Corporation | Elasticization of microporous woven tubes |
JPH0657244B2 (en) * | 1985-08-31 | 1994-08-03 | 京セラ株式会社 | Biomedical implant |
DE3640745A1 (en) * | 1985-11-30 | 1987-06-04 | Ernst Peter Prof Dr M Strecker | Catheter for producing or extending connections to or between body cavities |
US4665918A (en) * | 1986-01-06 | 1987-05-19 | Garza Gilbert A | Prosthesis system and method |
US4701291A (en) * | 1986-07-25 | 1987-10-20 | The Duriron Company, Inc. | Process of isostatic molding and bonding fluoropolymers |
JPS6395050A (en) * | 1986-10-08 | 1988-04-26 | 鐘淵化学工業株式会社 | Artificial blood vessel |
US4816339A (en) * | 1987-04-28 | 1989-03-28 | Baxter International Inc. | Multi-layered poly(tetrafluoroethylene)/elastomer materials useful for in vivo implantation |
US5061276A (en) * | 1987-04-28 | 1991-10-29 | Baxter International Inc. | Multi-layered poly(tetrafluoroethylene)/elastomer materials useful for in vivo implantation |
CS265167B1 (en) * | 1987-08-07 | 1989-10-13 | Rostislav Prochazka | Knitted smooth or wrapped vessel prosthese in warp weave |
US4892539A (en) * | 1988-02-08 | 1990-01-09 | D-R Medical Systems, Inc. | Vascular graft |
US5207705A (en) * | 1988-12-08 | 1993-05-04 | Brigham And Women's Hospital | Prosthesis of foam polyurethane and collagen and uses thereof |
US5152782A (en) * | 1989-05-26 | 1992-10-06 | Impra, Inc. | Non-porous coated ptfe graft |
US4955899A (en) * | 1989-05-26 | 1990-09-11 | Impra, Inc. | Longitudinally compliant vascular graft |
US5104400A (en) * | 1989-05-26 | 1992-04-14 | Impra, Inc. | Blood vessel patch |
US5100422A (en) * | 1989-05-26 | 1992-03-31 | Impra, Inc. | Blood vessel patch |
AU659097B2 (en) * | 1990-08-28 | 1995-05-11 | Meadox Medicals, Inc. | Self-supporting woven vascular graft |
US5178630A (en) * | 1990-08-28 | 1993-01-12 | Meadox Medicals, Inc. | Ravel-resistant, self-supporting woven graft |
SE9102448D0 (en) * | 1990-08-28 | 1991-08-26 | Meadox Medicals Inc | RAVEL RESISTANT, SELF-SUPPORTING WOVEN GRAFT |
US5713888A (en) * | 1990-10-31 | 1998-02-03 | Baxter International, Inc. | Tissue implant systems |
WO1992007525A1 (en) * | 1990-10-31 | 1992-05-14 | Baxter International Inc. | Close vascularization implant material |
US5733336A (en) * | 1990-10-31 | 1998-03-31 | Baxter International, Inc. | Ported tissue implant systems and methods of using same |
US5314471A (en) * | 1991-07-24 | 1994-05-24 | Baxter International Inc. | Tissue inplant systems and methods for sustaining viable high cell densities within a host |
US5344454A (en) * | 1991-07-24 | 1994-09-06 | Baxter International Inc. | Closed porous chambers for implanting tissue in a host |
US5453278A (en) * | 1991-07-24 | 1995-09-26 | Baxter International Inc. | Laminated barriers for tissue implants |
US6773458B1 (en) | 1991-07-24 | 2004-08-10 | Baxter International Inc. | Angiogenic tissue implant systems and methods |
US5211658A (en) * | 1991-11-05 | 1993-05-18 | New England Deaconess Hospital Corporation | Method and device for performing endovascular repair of aneurysms |
US5433748A (en) * | 1991-12-04 | 1995-07-18 | Porex Technologies Corp. | Auricular implant |
US5935122A (en) * | 1991-12-13 | 1999-08-10 | Endovascular Technologies, Inc. | Dual valve, flexible expandable sheath and method |
US5395349A (en) * | 1991-12-13 | 1995-03-07 | Endovascular Technologies, Inc. | Dual valve reinforced sheath and method |
US6808520B1 (en) | 1991-12-13 | 2004-10-26 | Endovascular Technologies, Inc. | Dual valve, flexible expandable sheath and method |
US6652492B1 (en) | 1991-12-13 | 2003-11-25 | Endovascular Technologies, Inc. | Dual valve, flexible sheath and method |
US5683448A (en) * | 1992-02-21 | 1997-11-04 | Boston Scientific Technology, Inc. | Intraluminal stent and graft |
US5405377A (en) * | 1992-02-21 | 1995-04-11 | Endotech Ltd. | Intraluminal stent |
ES2133393T3 (en) * | 1992-03-13 | 1999-09-16 | Atrium Medical Corp | FLUOROPOLYMER PRODUCTS (FOR EXAMPLE, POLITETRAFLUOROETHYLENE) EXPANDED OF CONTROLLED POROSITY AND ITS MANUFACTURE. |
US5282823A (en) * | 1992-03-19 | 1994-02-01 | Medtronic, Inc. | Intravascular radially expandable stent |
JP3335668B2 (en) * | 1992-06-12 | 2002-10-21 | テルモ株式会社 | Artificial blood vessel |
US5300115A (en) * | 1992-11-19 | 1994-04-05 | Keratos, Inc. | Intraocular prosthesis |
JPH0767895A (en) * | 1993-06-25 | 1995-03-14 | Sumitomo Electric Ind Ltd | Antimicrobial artificial blood vessel and suture yarn for antimicrobial operation |
CA2166797A1 (en) * | 1993-07-12 | 1995-01-26 | Robert Schindler | Soft tissue augmentation apparatus |
EP0670738A1 (en) * | 1993-09-24 | 1995-09-13 | Baxter International Inc. | Methods for enhancing vascularization of implant devices |
DE69433617T2 (en) | 1993-09-30 | 2005-03-03 | Endogad Research Pty Ltd. | INTRALUMINAL TRANSPLANT |
US6689158B1 (en) | 1993-09-30 | 2004-02-10 | Endogad Research Pty Limited | Intraluminal graft |
US5713950A (en) | 1993-11-01 | 1998-02-03 | Cox; James L. | Method of replacing heart valves using flexible tubes |
US5527353A (en) | 1993-12-02 | 1996-06-18 | Meadox Medicals, Inc. | Implantable tubular prosthesis |
US5609627A (en) | 1994-02-09 | 1997-03-11 | Boston Scientific Technology, Inc. | Method for delivering a bifurcated endoluminal prosthesis |
US6051020A (en) | 1994-02-09 | 2000-04-18 | Boston Scientific Technology, Inc. | Bifurcated endoluminal prosthesis |
US6165213A (en) * | 1994-02-09 | 2000-12-26 | Boston Scientific Technology, Inc. | System and method for assembling an endoluminal prosthesis |
US6039749A (en) | 1994-02-10 | 2000-03-21 | Endovascular Systems, Inc. | Method and apparatus for deploying non-circular stents and graftstent complexes |
WO1995031945A1 (en) | 1994-05-19 | 1995-11-30 | Scimed Life Systems, Inc. | Improved tissue supporting devices |
EP0686379B2 (en) | 1994-06-08 | 2007-03-28 | Cardiovascular Concepts, Inc. | Vascular graft |
US6156305A (en) * | 1994-07-08 | 2000-12-05 | Baxter International Inc. | Implanted tumor cells for the prevention and treatment of cancer |
US5556426A (en) * | 1994-08-02 | 1996-09-17 | Meadox Medicals, Inc. | PTFE implantable tubular prostheses with external coil support |
US6331188B1 (en) | 1994-08-31 | 2001-12-18 | Gore Enterprise Holdings, Inc. | Exterior supported self-expanding stent-graft |
US6015429A (en) | 1994-09-08 | 2000-01-18 | Gore Enterprise Holdings, Inc. | Procedures for introducing stents and stent-grafts |
US5782789A (en) * | 1994-10-19 | 1998-07-21 | Atrium Medical Corporation | Macrochannel phosthetic/delivery patch |
GB2298577B (en) | 1995-03-09 | 1999-02-17 | Univ Bristol | Arteriovenous bypass grafting |
US6451047B2 (en) | 1995-03-10 | 2002-09-17 | Impra, Inc. | Encapsulated intraluminal stent-graft and methods of making same |
US6264684B1 (en) | 1995-03-10 | 2001-07-24 | Impra, Inc., A Subsidiary Of C.R. Bard, Inc. | Helically supported graft |
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. |
BE1009277A3 (en) * | 1995-04-12 | 1997-01-07 | Corvita Europ | Guardian self-expandable medical device introduced in cavite body, and method of preparation. |
US6863686B2 (en) | 1995-04-17 | 2005-03-08 | Donald Shannon | Radially expandable tape-reinforced vascular grafts |
US5641373A (en) * | 1995-04-17 | 1997-06-24 | Baxter International Inc. | Method of manufacturing a radially-enlargeable PTFE tape-reinforced vascular graft |
US5628786A (en) * | 1995-05-12 | 1997-05-13 | Impra, Inc. | Radially expandable vascular graft with resistance to longitudinal compression and method of making same |
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 |
ES2206581T3 (en) * | 1995-06-07 | 2004-05-16 | Edwards Lifesciences Corporation | VASCULAR GRAFT WITH REINFORCEMENT TAPE AND EXTERNAL SUPPORT. |
US6010530A (en) * | 1995-06-07 | 2000-01-04 | Boston Scientific Technology, Inc. | Self-expanding endoluminal prosthesis |
US6099558A (en) * | 1995-10-10 | 2000-08-08 | Edwards Lifesciences Corp. | Intraluminal grafting of a bifuricated artery |
US5628788A (en) * | 1995-11-07 | 1997-05-13 | Corvita Corporation | Self-expanding endoluminal stent-graft |
US6042605A (en) | 1995-12-14 | 2000-03-28 | Gore Enterprose Holdings, Inc. | Kink resistant stent-graft |
EP0866677A4 (en) | 1995-12-14 | 1999-10-27 | Prograft Medical Inc | Stent-graft deployment apparatus and method |
US6428571B1 (en) | 1996-01-22 | 2002-08-06 | Scimed Life Systems, Inc. | Self-sealing PTFE vascular graft and manufacturing methods |
US5800512A (en) | 1996-01-22 | 1998-09-01 | Meadox Medicals, Inc. | PTFE vascular graft |
US5607478A (en) * | 1996-03-14 | 1997-03-04 | Meadox Medicals Inc. | Yarn wrapped PTFE tubular prosthesis |
CA2199890C (en) * | 1996-03-26 | 2002-02-05 | Leonard Pinchuk | Stents and stent-grafts having enhanced hoop strength and methods of making the same |
US5800514A (en) * | 1996-05-24 | 1998-09-01 | Meadox Medicals, Inc. | Shaped woven tubular soft-tissue prostheses and methods of manufacturing |
US5968068A (en) * | 1996-09-12 | 1999-10-19 | Baxter International Inc. | Endovascular delivery system |
US5925074A (en) | 1996-12-03 | 1999-07-20 | Atrium Medical Corporation | Vascular endoprosthesis and method |
US5897587A (en) | 1996-12-03 | 1999-04-27 | Atrium Medical Corporation | Multi-stage prosthesis |
US6010529A (en) | 1996-12-03 | 2000-01-04 | Atrium Medical Corporation | Expandable shielded vessel support |
US6416537B1 (en) | 1996-12-03 | 2002-07-09 | Atrium Medical Corporation | Multi-stage prosthesis |
US6352561B1 (en) | 1996-12-23 | 2002-03-05 | W. L. Gore & Associates | Implant deployment apparatus |
US6551350B1 (en) | 1996-12-23 | 2003-04-22 | Gore Enterprise Holdings, Inc. | Kink resistant bifurcated prosthesis |
US6682745B1 (en) | 1998-07-28 | 2004-01-27 | Christiaan Antonius Arnoldus Jacobs | Use of bacterium for manufacture of a vaccine |
US6070589A (en) | 1997-08-01 | 2000-06-06 | Teramed, Inc. | Methods for deploying bypass graft stents |
US6626938B1 (en) | 2000-11-16 | 2003-09-30 | Cordis Corporation | Stent graft having a pleated graft member |
US6887268B2 (en) | 1998-03-30 | 2005-05-03 | Cordis Corporation | Extension prosthesis for an arterial repair |
US6290731B1 (en) | 1998-03-30 | 2001-09-18 | Cordis Corporation | Aortic graft having a precursor gasket for repairing an abdominal aortic aneurysm |
US7118600B2 (en) | 1998-08-31 | 2006-10-10 | Wilson-Cook Medical, Inc. | Prosthesis having a sleeve valve |
US6746489B2 (en) | 1998-08-31 | 2004-06-08 | Wilson-Cook Medical Incorporated | Prosthesis having a sleeve valve |
US6540780B1 (en) * | 1998-11-23 | 2003-04-01 | Medtronic, Inc. | Porous synthetic vascular grafts with oriented ingrowth channels |
US7049380B1 (en) * | 1999-01-19 | 2006-05-23 | Gore Enterprise Holdings, Inc. | Thermoplastic copolymer of tetrafluoroethylene and perfluoromethyl vinyl ether and medical devices employing the copolymer |
ATE257713T1 (en) | 1999-01-26 | 2004-01-15 | Akzo Nobel Nv | USE OF LIVE ATTENUATE BACTERIA TO PRODUCE A SUBMUCOSAL VACCINE |
US6398803B1 (en) | 1999-02-02 | 2002-06-04 | Impra, Inc., A Subsidiary Of C.R. Bard, Inc. | Partial encapsulation of stents |
US6689160B1 (en) | 1999-05-31 | 2004-02-10 | Sumitomo Electric Industries, Ltd. | Prosthesis for blood vessel |
US6344056B1 (en) | 1999-12-29 | 2002-02-05 | Edwards Lifesciences Corp. | Vascular grafts for bridging a vessel side branch |
US6663667B2 (en) | 1999-12-29 | 2003-12-16 | Edwards Lifesciences Corporation | Towel graft means for enhancing tissue ingrowth in vascular grafts |
US6312458B1 (en) * | 2000-01-19 | 2001-11-06 | Scimed Life Systems, Inc. | Tubular structure/stent/stent securement member |
US6355063B1 (en) | 2000-01-20 | 2002-03-12 | Impra, Inc. | Expanded PTFE drug delivery graft |
US6245100B1 (en) | 2000-02-01 | 2001-06-12 | Cordis Corporation | Method for making a self-expanding stent-graft |
US6296661B1 (en) | 2000-02-01 | 2001-10-02 | Luis A. Davila | Self-expanding stent-graft |
CA2402504A1 (en) | 2000-03-10 | 2001-09-20 | Paracor Surgical, Inc. | Expandable cardiac harness for treating congestive heart failure |
WO2002015951A2 (en) | 2000-08-23 | 2002-02-28 | Thoratec Corporation | Coated vascular grafts and methods of use |
US7314483B2 (en) | 2000-11-16 | 2008-01-01 | Cordis Corp. | Stent graft with branch leg |
US6942692B2 (en) | 2000-11-16 | 2005-09-13 | Cordis Corporation | Supra-renal prosthesis and renal artery bypass |
US7267685B2 (en) | 2000-11-16 | 2007-09-11 | Cordis Corporation | Bilateral extension prosthesis and method of delivery |
US7229472B2 (en) | 2000-11-16 | 2007-06-12 | Cordis Corporation | Thoracic aneurysm repair prosthesis and system |
US6843802B1 (en) | 2000-11-16 | 2005-01-18 | Cordis Corporation | Delivery apparatus for a self expanding retractable stent |
DE10061936A1 (en) * | 2000-12-13 | 2002-07-04 | Valentin Kramer | Object from ePTFE and method of manufacturing the same |
US20030017775A1 (en) * | 2001-06-11 | 2003-01-23 | Scimed Life Systems. Inc.. | Composite ePTFE/textile prosthesis |
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 |
EP1414369A2 (en) * | 2001-07-27 | 2004-05-06 | Medtronic, Inc. | Adventitial fabric reinforced porous prosthetic graft |
JP2005501652A (en) | 2001-09-10 | 2005-01-20 | パラコー メディカル インコーポレイテッド | Heart failure treatment device |
CA2460307A1 (en) | 2001-10-31 | 2003-05-08 | Paracor Medical, Inc. | Heart failure treatment device |
US7174896B1 (en) | 2002-01-07 | 2007-02-13 | Paracor Medical, Inc. | Method and apparatus for supporting a heart |
US7022063B2 (en) | 2002-01-07 | 2006-04-04 | Paracor Medical, Inc. | Cardiac harness |
US7326237B2 (en) | 2002-01-08 | 2008-02-05 | Cordis Corporation | Supra-renal anchoring prosthesis |
DE60336658D1 (en) | 2002-07-17 | 2011-05-19 | Proxy Biomedical Ltd | Membrane for medical implantation |
US20040024448A1 (en) | 2002-08-05 | 2004-02-05 | Chang James W. | Thermoplastic fluoropolymer-coated medical devices |
WO2004021927A2 (en) | 2002-09-05 | 2004-03-18 | Paracor Medical, Inc. | Cardiac harness |
EP1560541A2 (en) | 2002-11-15 | 2005-08-10 | Paracor Medical, Inc. | Cardiac harness delivery device |
US7229405B2 (en) | 2002-11-15 | 2007-06-12 | Paracor Medical, Inc. | Cardiac harness delivery device and method of use |
US7736299B2 (en) | 2002-11-15 | 2010-06-15 | Paracor Medical, Inc. | Introducer for a cardiac harness delivery |
US20070276179A1 (en) * | 2002-11-15 | 2007-11-29 | Paracor Medical, Inc. | Method of loading a cardiac harness in a housing |
CA2530429A1 (en) | 2003-07-10 | 2005-01-27 | Paracor Medical, Inc. | Self-anchoring cardiac harness |
US7155295B2 (en) | 2003-11-07 | 2006-12-26 | Paracor Medical, Inc. | Cardiac harness for treating congestive heart failure and for defibrillating and/or pacing/sensing |
US7158839B2 (en) | 2003-11-07 | 2007-01-02 | Paracor Medical, Inc. | Cardiac harness for treating heart disease |
JP2007518490A (en) | 2004-01-12 | 2007-07-12 | パラコー メディカル インコーポレイテッド | Cardiac harness with interconnecting strands |
US7794490B2 (en) * | 2004-06-22 | 2010-09-14 | Boston Scientific Scimed, Inc. | Implantable medical devices with antimicrobial and biodegradable matrices |
CA2577108A1 (en) | 2004-08-31 | 2006-03-09 | C.R. Bard, Inc. | Self-sealing ptfe graft with kink resistance |
US8029563B2 (en) | 2004-11-29 | 2011-10-04 | Gore Enterprise Holdings, Inc. | Implantable devices with reduced needle puncture site leakage |
ES2625807T3 (en) | 2005-06-17 | 2017-07-20 | C.R. Bard, Inc. | Vascular graft with twisting resistance after clamping |
US7587247B2 (en) | 2005-08-01 | 2009-09-08 | Paracor Medical, Inc. | Cardiac harness having an optimal impedance range |
EP1937183B1 (en) * | 2005-09-12 | 2018-11-28 | Proxy Biomedical Limited | Soft tissue implants |
WO2007056762A2 (en) * | 2005-11-09 | 2007-05-18 | C.R. Bard Inc. | Grafts and stent grafts having a radiopaque beading |
WO2007056761A2 (en) * | 2005-11-09 | 2007-05-18 | C.R. Bard Inc. | Grafts and stent grafts having a radiopaque marker |
JP4821466B2 (en) * | 2006-07-03 | 2011-11-24 | 富士ゼロックス株式会社 | Droplet discharge head |
WO2008063780A2 (en) * | 2006-10-12 | 2008-05-29 | C.R. Bard Inc. | Vascular grafts with multiple channels and methods for making |
WO2008076383A2 (en) | 2006-12-18 | 2008-06-26 | Med Institute Inc. | Stent graft with releasable therapeutic agent |
US8221505B2 (en) | 2007-02-22 | 2012-07-17 | Cook Medical Technologies Llc | Prosthesis having a sleeve valve |
US8192351B2 (en) | 2007-08-13 | 2012-06-05 | Paracor Medical, Inc. | Medical device delivery system having integrated introducer |
EP2200931B1 (en) * | 2007-09-19 | 2017-06-07 | The Charles Stark Draper Laboratory, Inc. | Microfluidic structures with circular cross-section |
US7733137B2 (en) * | 2007-10-16 | 2010-06-08 | International Business Machines Corporation | Design structures including multiple reference frequency fractional-N PLL (phase locked loop) |
US8196279B2 (en) | 2008-02-27 | 2012-06-12 | C. R. Bard, Inc. | Stent-graft covering process |
US8343136B2 (en) * | 2008-08-26 | 2013-01-01 | Cook Medical Technologies Llc | Introducer sheath with encapsulated reinforcing member |
US8696738B2 (en) | 2010-05-20 | 2014-04-15 | Maquet Cardiovascular Llc | Composite prosthesis with external polymeric support structure and methods of manufacturing the same |
US9814560B2 (en) | 2013-12-05 | 2017-11-14 | W. L. Gore & Associates, Inc. | Tapered implantable device and methods for making such devices |
JP6673942B2 (en) | 2015-06-05 | 2020-04-01 | ダブリュ.エル.ゴア アンド アソシエイツ,インコーポレイティドW.L. Gore & Associates, Incorporated | Tapered hypobleeding implantable prosthesis |
Family Cites Families (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3105492A (en) * | 1958-10-01 | 1963-10-01 | Us Catheter & Instr Corp | Synthetic blood vessel grafts |
GB1104680A (en) * | 1965-10-18 | 1968-02-28 | Univ Birmingham | Artificial artery |
US3479670A (en) * | 1966-10-19 | 1969-11-25 | Ethicon Inc | Tubular prosthetic implant having helical thermoplastic wrapping therearound |
FR2248015A1 (en) * | 1973-10-17 | 1975-05-16 | Rhone Poulenc Ind | Artificial ureter or urethra - watertight flexible tube has helical rib in outside wall to prevent creasing |
AR205110A1 (en) * | 1974-04-02 | 1976-04-05 | Gore & Ass | ARTIFICIAL VASCULAR PROSTHESIS |
JPS5413694A (en) * | 1977-07-01 | 1979-02-01 | Sumitomo Electric Industries | Composite blood vessel prosthesis and method of producing same |
-
1978
- 1978-10-12 JP JP53125953A patent/JPS6037734B2/en not_active Expired
-
1979
- 1979-10-10 GB GB7935249A patent/GB2033233B/en not_active Expired
- 1979-10-10 IT IT50512/79A patent/IT1164833B/en active
- 1979-10-11 BE BE0/197600A patent/BE879355A/en not_active IP Right Cessation
- 1979-10-11 SE SE7908447A patent/SE7908447L/en unknown
- 1979-10-11 NL NLAANVRAGE7907531,A patent/NL173135C/en not_active IP Right Cessation
- 1979-10-11 DE DE19792941279 patent/DE2941279A1/en not_active Ceased
- 1979-10-11 AU AU51693/79A patent/AU527117B2/en not_active Expired
- 1979-10-12 US US06/084,325 patent/US4306318A/en not_active Ceased
- 1979-10-12 FR FR7925493A patent/FR2438472A1/en active Granted
- 1979-10-12 CA CA000337440A patent/CA1143105A/en not_active Expired
-
1982
- 1982-04-19 US US06/369,962 patent/USRE31618E/en not_active Expired - Lifetime
Also Published As
Publication number | Publication date |
---|---|
US4306318A (en) | 1981-12-22 |
GB2033233A (en) | 1980-05-21 |
IT1164833B (en) | 1987-04-15 |
AU5169379A (en) | 1980-04-17 |
NL173135C (en) | 1983-12-16 |
NL173135B (en) | 1983-07-18 |
GB2033233B (en) | 1983-05-11 |
FR2438472B1 (en) | 1984-11-30 |
JPS6037734B2 (en) | 1985-08-28 |
JPS5552755A (en) | 1980-04-17 |
USRE31618E (en) | 1984-07-03 |
DE2941279A1 (en) | 1980-04-17 |
SE7908447L (en) | 1980-04-13 |
FR2438472A1 (en) | 1980-05-09 |
BE879355A (en) | 1980-02-01 |
IT7950512A0 (en) | 1979-10-10 |
NL7907531A (en) | 1980-04-15 |
AU527117B2 (en) | 1983-02-17 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA1143105A (en) | Tubular organic prosthesis and process for production thereof | |
US4332035A (en) | Porous structure of polytetrafluoroethylene and process for production thereof | |
US4713070A (en) | Porous structure of polytetrafluoroethylene and process for production thereof | |
CA1140704A (en) | Tubular organic prothesis and process for the production thereof | |
US4652263A (en) | Elasticization of microporous woven tubes | |
EP0656196B1 (en) | Implantable tubular prosthesis | |
US5071609A (en) | Process of manufacturing porous multi-expanded fluoropolymers | |
US5910168A (en) | Prosthetic vascular graft | |
US4321711A (en) | Vascular prosthesis | |
EP0256748A2 (en) | Porous highly expanded fluoropolymers and a process for preparing them | |
US20020111667A1 (en) | Non-expanded porous polytetrafluoroethylene (PTFE) products and methods of manufacture | |
Leidner et al. | A novel process for the manufacturing of porous grafts: Process description and product evaluation | |
US3337673A (en) | Uniformly corrugated prosthesis and process of making same | |
Khlif et al. | Contribution to the improvement of textile vascular prostheses crimping | |
EP0269449A2 (en) | Porous flexible radially expanded fluoropolymers and process for producing the same | |
JPS62152470A (en) | Tubular organ prosthetic material | |
JP2007519445A (en) | Method for manufacturing an artificial joint | |
US4596577A (en) | Napped fluororesin materials having continuous pores, and a method of manufacturing the same | |
JPH0242656B2 (en) | ||
EP0352972A2 (en) | Fiber-reinforced expanded fluoroplastic vascular grafts | |
JP2814415B2 (en) | Artificial blood vessel and its manufacturing method | |
JPS62152467A (en) | Production of tubular organ prosthetic material | |
CN210124875U (en) | Small-caliber bionic blood vessel with three-layer structure | |
Williams et al. | The Mechanical and Microscopic Aspects of the Deformation and Fracture of a Poly (Ether Urethane-Urea) Spun Arterial Prosthesis | |
JPH01242068A (en) | Medical tubular body excellent in antithrombogenicity and preparation thereof |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
MKEX | Expiry |