CA1292597C - Tubular prothesis having a composite structure - Google Patents
Tubular prothesis having a composite structureInfo
- Publication number
- CA1292597C CA1292597C CA000525434A CA525434A CA1292597C CA 1292597 C CA1292597 C CA 1292597C CA 000525434 A CA000525434 A CA 000525434A CA 525434 A CA525434 A CA 525434A CA 1292597 C CA1292597 C CA 1292597C
- Authority
- CA
- Canada
- Prior art keywords
- tube
- tubular
- composite structure
- polytetrafluoroethylene
- collagen
- 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
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/28—Materials for coating prostheses
- A61L27/34—Macromolecular materials
-
- 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
ABSTRACT OF THE DISCLOSURE
A tubular prosthesis having a composite structure comprising (i) tubular polytetrafluoroethylene having a microfibrous structure comprising small nodes interconnected with fibrils and (ii) materials which can be absorbed by a living body wherein (a) said polytetrafluoroethylene has a greater average fibril length on the outer surface than on the inner surface, and the fibrous structure of said polytetrafluoroethylene varies continuously across the thickness of the tube wall wherein said inner surface has said fibrous structure being predominantly oriented along the axial direction and said outer surface has said fibrous structure being predominantly oriented along the concentric direction; and (b) said materials which can be absorbed by a living body are collagen, at least one of albumin and chitosan, and heparin, and are distributed in such a manner that collagen is present in the portion of the tube wall which is closest to the outer surface thereof while at least one of albumin and chitosan is present in the portion of the tube wall which is closest to the inner surface thereof, and heparin is present in the inner surface of the tube wall.
A tubular prosthesis having a composite structure comprising (i) tubular polytetrafluoroethylene having a microfibrous structure comprising small nodes interconnected with fibrils and (ii) materials which can be absorbed by a living body wherein (a) said polytetrafluoroethylene has a greater average fibril length on the outer surface than on the inner surface, and the fibrous structure of said polytetrafluoroethylene varies continuously across the thickness of the tube wall wherein said inner surface has said fibrous structure being predominantly oriented along the axial direction and said outer surface has said fibrous structure being predominantly oriented along the concentric direction; and (b) said materials which can be absorbed by a living body are collagen, at least one of albumin and chitosan, and heparin, and are distributed in such a manner that collagen is present in the portion of the tube wall which is closest to the outer surface thereof while at least one of albumin and chitosan is present in the portion of the tube wall which is closest to the inner surface thereof, and heparin is present in the inner surface of the tube wall.
Description
25i97 T~ JLAR P~OST~IESIS EIAVI2~G A COMPOSITE STRUCTURE
FIELD OF THE INVENTION
The present invention relates to a tubular prosthesis comprising a polytetrafluoroethylene (PTFE) porous tube ha~ing improved tube strength and ability to bind with body tissues. More specifically, the present invention also relates to a tubular prosthesis having a composite structure comprising PTFE with a specified fibrous structure and a material which can be absorbed by a living body.
BACKGROUND OF T~IE INV~:NTION
PTFE porous tubes made by a stretching method have be n usei as tubular prostheses, and many cases of the clinical application o sucb tubes as ar~ificial blood vessels have been reported. Such PT~ porous tubes are su~erior over conventional prostheses made of knitted or woven fabrics. The stretched PTFE tube has a microfibrous structure con;isting of small nodes interconnected with many thin fibrils. The diameter of the fibrils, which depends on the conditions of the stretching or drawing operations employed, can be made much smaller than the filaments in the knitted or woven fabrics. In addition, because their pore size and porosity can be freely controlled, the PTFE tubes are flexible and can be used as substitutes for tubular organs such as blood vessels with ~2~Z5~
1 little chance of thrombus formation. In addition to these advantages, the PTFE tubes allow pseudo-intima to form on the surfaces of the internal cavities thereof without causing any damage in the surrounding tissues~ For these reasons, the stretched PT~E tubes are considered to be one of the most promising prostheses for replacement of tubular organs.
Relatively large tubes having an inner diameter of 6 mm or more have been demonstrated to perform well as ~o artificial blood vessels, but with narrower tubes having an inner diameter oE S mm or less, growth of thrombi occuring on the inner surfaces thereof, particulzrly at the sites where the tubes are sutured with host blood vessels has been reported. Therefore, at the present time there are no PTFE tubes available to replace any sIood vessel, particularly blood vessels having an inner diameter of less t~an 5 mm, more particularly as narrow as 1 to 3 mm even i the tube has the same fibril structure as the artificial blood vessels having an inner diameter of 6 mm or more.
SUMMARY OF THE INVENTION
-Therefore, an object of the present invention is to provide a prosthesis having excellent compatibility with a living body, particularly to provide a tublar prosthesis excellent in compatibility even i it has an inner diameter of less than 5 mm, particularly as narrow ~Z~5~7 1 as from 1 to 3 mm.
As the results of the extensive research made by the present inventors, the above and other objects of the present invention have been attained by a tubular prosthesis having a composite structure comprising a combination of a PTFE material having a specific fibrous structure and one or more materials which exist in important organs in a living body and which hence are absorbed by a body through metabolism. More specifically the above and the other objects of the present invention have been attained by a tubular prosthesis having a composi.e Ctructure comprising (i) tUbulz-polytetrafluoroethylene having a microfibrous struc~ure comprising small nodes interconnected with fibrils and (ii) materials which can be absorbed by a living body wherein (a) s~id polytetrafluoroethylene has a greater average fibril length on the outer surface than on the inner surface, and the fibrous structure of said polytetrafluoroethylene varies continuously across the thickness of the tube wall, wherein said inner surface has said fibrous structure being predominantly oriented along the axial direction ana saia outer surface has said fibrous structure being predominantly oriented along the concentric direction; and (b) said materials which can be absorbed by a living body are collagen, at least one of albumin and chitosan, and heparin, and are distributed in l such a manner that collagen is present in the portion o~
the tube wall which is closest to the outer surface thereof, wh;le at least one of albumin and chitosan is present in the portion of the tube wall which is closest to the inner surface thereof, and heparin is present in the inner surface of the tube wall.
DET~ILED DESCRIPTION OF THE INVENTION
When the surface of a fibrous stru~ture solely made of PTFE is in contact with the blood, undesirable amounts of proteins will ~uild up on the contacted surface. This is accompanied by cohesion of platelets and adhesion of fibrins which causes the clotting of blood to proceed until thrombi~ form. The thrombi are responsible for the formation of emboli in tubular prostheses with small diameters.
Heparin has the ability to retard the clo~ing of the blood and is used as an anticoagulant in ~arious forms. U.S. I~atent 3,441,142 discloses a thin film or the reaction product of an alkali metal salt of heparin with a polymer containing quaternized nitrogen atoms. U.S.
Patent 3,755,218 discloses the reaction product of polyurethane with heparin. U.S. Patent 3,475,410 discloses a method for forming a composite membrane surface by introducing amino groups into a cellulose film and subsequent heparinization. These references have succeeded to some extent in retarding thrombus formation 3 ~ 7 1 but they are incapable of providiny tubular prostheses suitable for long-term implantation in a li~ing bod~
In accordance with the present invention, a PTFE
tube having a fibrous structure is used as a material which exhibits high resistance to blood clotting during prolonged transplantation into the body; albumin which is a construction material of the blood and/or chitosan which is a biopolymer is used to the assist in the binding of heparin to th~ PTF~ tube; and collagen which is also a blopolymer is incorporated in order to promote the penetration and growth o~ fibroblasts and other tissues in the transplant~d PTFE tube.
The me~hod using albumin as a heparin binder is disclosed irl Japanese Patent Application (O?I) No. 118761J83 (the term "OPI~ as used hereinaf~er means an une~amined published Japanese patent aplication) but does not disclose artificial tubular organs intended for long~
term transplantation into the body. The use of chitosan as a heparin binder is disclosed in Japanese Patent Application (OPI) No. 89868/82 but its applicaton is limited to catheters and renal dialyzers and no reference is made to artificial tubular organs intended for long-term transplantation. The application of collagen to the outer portion of the fibrous structure of PTFE is disclosed in Japanese Patent Application (OPI) No. 106164/80, but in this method, it is re~uired to 1 distribute a silicone material over the surface which is in contact with blood.
Succinylation of collagen at the surface per se as a method for preventing blood clotting is disclosed in 5Japanese Paten~: ~pplica~ion (OPI) No. 165854/83. Collagen can be bound to heparin by the use of protamine or protamine sulfate as shown in Japanese Patent Application ~OPI) No, 180162/83. However, there is no teaching therein of a ~TFE tube that has both a fibrous structure and the distribution profile of the additional components contemplated by the present invention wherein collagen is present in the portion of the tube wall which is closest to the outer ~urface thereof and albumin and/or chitosan i' is presen~ in the portion of the tube wall whicn is closest to the inne~ surface thereoE, and heparin is present only in the inner surface of the tube wall, wherein the heparln is bound to the albumin and/or chitosan.
One problem associated with the use of stretched PTFE porous tubes as tubular prostheses is that they have a tendency to be torn apart by suture needles or lines which are employed ,to join the tubes with a living tissues. PTFE tubes frequently tear in the axial direction probably because the microfibrous str.ucture of PTFE is predominantly oriented in the axial direction by stretching. In order to render PTFE tubes resistant to ~2~2~7 1 tearing, it has been proposed that a PT~E porous tape or fibers of other materials be wrapped helically onto the tube to provide an integral body. This approach is intended to prevent the tube from tearing in t'ne axial direction by providing the outer surface of the tube with the concentric orientation, and differs from the concept of the present invention which provides a tubular prosthesis in the form of a single tube in which the fibrous structure is oriented both in the axial and concentric directionsO In acco~dance with the present invention, the problenl of tube tearing is solved b~
causing the fibrous structure of PTFE to vary continuously across the wall thickness including the inner surface which is predominantly oriented in the axial direction and the outer surEace which is predominantly oriented in the concentric direction. Another problem which has precluded commercial application of the conventional PTFE porous tubes is that: if they are bent into a small-diameter cylinder they buc'cle and fail to maintain the cylindrical shape. This problem is also soived by the tubular prosthesis of the present invention which has sufficient concentric orientation in the outer surface thereof to avoid buckling upon bending. The use of the conventional PTFE porous tubes as tubular prostheses has also failed to achieve anything more than limited success because of their restricted ability to bind with the surrounding J.Z9;25~37 1 tissues. The PTFE tube of the present in~ention has a larger average pore size in the outer surEace than in the inner surface, and this provides enhanced organization of the surrounding tissues by facilitating their ingress into the tube and subsequent binding therewit'n. In this respect, collagen which is present in both the interior and the outer surface of the fibrous structure of the tube is particularly effec~ive in promoting the penetration of fibroblasts t~rough the tube wall and promoting their growth in the tube.
The PTFE porous tube which can be used in the present invent:ion may oe produced by a method which i5 basically the same as the one described in Japanese Patent Publication No. 1~560~67. The method comprises the step in which a mixture- o an unsintered ~TF~ powder and a liquid lubricant is supplied into a ram ex.ruder to extrude in a tubular form, the tube thus obtained is then stretched in the axial direction, with radial expansion being optionally achieved simultaneously or afterward, while the liquid lubricant is or is not removed from the tube; thereafter while the stretched tube is fixed to prevent shrinkage, the stretched tube is sintered by heating to a sintering temperature of 327C ox more to fix the stretched structure.
Examples of the liquid lublicant used in the present invention include those described in Japanese 1 Patent Publication No. 13560/67.
The resulting PTFE porous tube provided with increased strength has a microfibrous structure comprising small nodes interconnected with many thin fibrils. The diameter and length of the fibrils and the size and number of the nodes can be varied by changing the conditions of stretching and sintering operations, and thus the pore size and porosity of ~he porous tube thus obtained can be freely controlled. It has been clinically reported that when this type of porous tube i~ used as an artificial blood vessel, it preferably has an average pore size of from 1 to LOO micrometers, a porosi~y of 70% or more, and a tube wall thickness of from 0.3 to 1.0 mm.
The PTFE porous tube prodused by the method described a~ove is typically characte~izea in that the fibrous structure of PT~E is predominan ly oriented in the - axial direction. In accordance with the present invention, the stretched tube is sintered, while being fixed to prevent thermal shrinkage, by heating the outer surface of the tube to a temperature of 327C or higher until it acquires a meshed or network-like structure. By this process, the outer surface of the tube attains a larger 2verase pore size than the inner surface and the fibrous structure of PTFE is caused to vary continuously across the wall thickness from the inner surface which is predominantly oriented along the axial direction to the g _ ;
;
FIELD OF THE INVENTION
The present invention relates to a tubular prosthesis comprising a polytetrafluoroethylene (PTFE) porous tube ha~ing improved tube strength and ability to bind with body tissues. More specifically, the present invention also relates to a tubular prosthesis having a composite structure comprising PTFE with a specified fibrous structure and a material which can be absorbed by a living body.
BACKGROUND OF T~IE INV~:NTION
PTFE porous tubes made by a stretching method have be n usei as tubular prostheses, and many cases of the clinical application o sucb tubes as ar~ificial blood vessels have been reported. Such PT~ porous tubes are su~erior over conventional prostheses made of knitted or woven fabrics. The stretched PTFE tube has a microfibrous structure con;isting of small nodes interconnected with many thin fibrils. The diameter of the fibrils, which depends on the conditions of the stretching or drawing operations employed, can be made much smaller than the filaments in the knitted or woven fabrics. In addition, because their pore size and porosity can be freely controlled, the PTFE tubes are flexible and can be used as substitutes for tubular organs such as blood vessels with ~2~Z5~
1 little chance of thrombus formation. In addition to these advantages, the PTFE tubes allow pseudo-intima to form on the surfaces of the internal cavities thereof without causing any damage in the surrounding tissues~ For these reasons, the stretched PT~E tubes are considered to be one of the most promising prostheses for replacement of tubular organs.
Relatively large tubes having an inner diameter of 6 mm or more have been demonstrated to perform well as ~o artificial blood vessels, but with narrower tubes having an inner diameter oE S mm or less, growth of thrombi occuring on the inner surfaces thereof, particulzrly at the sites where the tubes are sutured with host blood vessels has been reported. Therefore, at the present time there are no PTFE tubes available to replace any sIood vessel, particularly blood vessels having an inner diameter of less t~an 5 mm, more particularly as narrow as 1 to 3 mm even i the tube has the same fibril structure as the artificial blood vessels having an inner diameter of 6 mm or more.
SUMMARY OF THE INVENTION
-Therefore, an object of the present invention is to provide a prosthesis having excellent compatibility with a living body, particularly to provide a tublar prosthesis excellent in compatibility even i it has an inner diameter of less than 5 mm, particularly as narrow ~Z~5~7 1 as from 1 to 3 mm.
As the results of the extensive research made by the present inventors, the above and other objects of the present invention have been attained by a tubular prosthesis having a composite structure comprising a combination of a PTFE material having a specific fibrous structure and one or more materials which exist in important organs in a living body and which hence are absorbed by a body through metabolism. More specifically the above and the other objects of the present invention have been attained by a tubular prosthesis having a composi.e Ctructure comprising (i) tUbulz-polytetrafluoroethylene having a microfibrous struc~ure comprising small nodes interconnected with fibrils and (ii) materials which can be absorbed by a living body wherein (a) s~id polytetrafluoroethylene has a greater average fibril length on the outer surface than on the inner surface, and the fibrous structure of said polytetrafluoroethylene varies continuously across the thickness of the tube wall, wherein said inner surface has said fibrous structure being predominantly oriented along the axial direction ana saia outer surface has said fibrous structure being predominantly oriented along the concentric direction; and (b) said materials which can be absorbed by a living body are collagen, at least one of albumin and chitosan, and heparin, and are distributed in l such a manner that collagen is present in the portion o~
the tube wall which is closest to the outer surface thereof, wh;le at least one of albumin and chitosan is present in the portion of the tube wall which is closest to the inner surface thereof, and heparin is present in the inner surface of the tube wall.
DET~ILED DESCRIPTION OF THE INVENTION
When the surface of a fibrous stru~ture solely made of PTFE is in contact with the blood, undesirable amounts of proteins will ~uild up on the contacted surface. This is accompanied by cohesion of platelets and adhesion of fibrins which causes the clotting of blood to proceed until thrombi~ form. The thrombi are responsible for the formation of emboli in tubular prostheses with small diameters.
Heparin has the ability to retard the clo~ing of the blood and is used as an anticoagulant in ~arious forms. U.S. I~atent 3,441,142 discloses a thin film or the reaction product of an alkali metal salt of heparin with a polymer containing quaternized nitrogen atoms. U.S.
Patent 3,755,218 discloses the reaction product of polyurethane with heparin. U.S. Patent 3,475,410 discloses a method for forming a composite membrane surface by introducing amino groups into a cellulose film and subsequent heparinization. These references have succeeded to some extent in retarding thrombus formation 3 ~ 7 1 but they are incapable of providiny tubular prostheses suitable for long-term implantation in a li~ing bod~
In accordance with the present invention, a PTFE
tube having a fibrous structure is used as a material which exhibits high resistance to blood clotting during prolonged transplantation into the body; albumin which is a construction material of the blood and/or chitosan which is a biopolymer is used to the assist in the binding of heparin to th~ PTF~ tube; and collagen which is also a blopolymer is incorporated in order to promote the penetration and growth o~ fibroblasts and other tissues in the transplant~d PTFE tube.
The me~hod using albumin as a heparin binder is disclosed irl Japanese Patent Application (O?I) No. 118761J83 (the term "OPI~ as used hereinaf~er means an une~amined published Japanese patent aplication) but does not disclose artificial tubular organs intended for long~
term transplantation into the body. The use of chitosan as a heparin binder is disclosed in Japanese Patent Application (OPI) No. 89868/82 but its applicaton is limited to catheters and renal dialyzers and no reference is made to artificial tubular organs intended for long-term transplantation. The application of collagen to the outer portion of the fibrous structure of PTFE is disclosed in Japanese Patent Application (OPI) No. 106164/80, but in this method, it is re~uired to 1 distribute a silicone material over the surface which is in contact with blood.
Succinylation of collagen at the surface per se as a method for preventing blood clotting is disclosed in 5Japanese Paten~: ~pplica~ion (OPI) No. 165854/83. Collagen can be bound to heparin by the use of protamine or protamine sulfate as shown in Japanese Patent Application ~OPI) No, 180162/83. However, there is no teaching therein of a ~TFE tube that has both a fibrous structure and the distribution profile of the additional components contemplated by the present invention wherein collagen is present in the portion of the tube wall which is closest to the outer ~urface thereof and albumin and/or chitosan i' is presen~ in the portion of the tube wall whicn is closest to the inne~ surface thereoE, and heparin is present only in the inner surface of the tube wall, wherein the heparln is bound to the albumin and/or chitosan.
One problem associated with the use of stretched PTFE porous tubes as tubular prostheses is that they have a tendency to be torn apart by suture needles or lines which are employed ,to join the tubes with a living tissues. PTFE tubes frequently tear in the axial direction probably because the microfibrous str.ucture of PTFE is predominantly oriented in the axial direction by stretching. In order to render PTFE tubes resistant to ~2~2~7 1 tearing, it has been proposed that a PT~E porous tape or fibers of other materials be wrapped helically onto the tube to provide an integral body. This approach is intended to prevent the tube from tearing in t'ne axial direction by providing the outer surface of the tube with the concentric orientation, and differs from the concept of the present invention which provides a tubular prosthesis in the form of a single tube in which the fibrous structure is oriented both in the axial and concentric directionsO In acco~dance with the present invention, the problenl of tube tearing is solved b~
causing the fibrous structure of PTFE to vary continuously across the wall thickness including the inner surface which is predominantly oriented in the axial direction and the outer surEace which is predominantly oriented in the concentric direction. Another problem which has precluded commercial application of the conventional PTFE porous tubes is that: if they are bent into a small-diameter cylinder they buc'cle and fail to maintain the cylindrical shape. This problem is also soived by the tubular prosthesis of the present invention which has sufficient concentric orientation in the outer surface thereof to avoid buckling upon bending. The use of the conventional PTFE porous tubes as tubular prostheses has also failed to achieve anything more than limited success because of their restricted ability to bind with the surrounding J.Z9;25~37 1 tissues. The PTFE tube of the present in~ention has a larger average pore size in the outer surEace than in the inner surface, and this provides enhanced organization of the surrounding tissues by facilitating their ingress into the tube and subsequent binding therewit'n. In this respect, collagen which is present in both the interior and the outer surface of the fibrous structure of the tube is particularly effec~ive in promoting the penetration of fibroblasts t~rough the tube wall and promoting their growth in the tube.
The PTFE porous tube which can be used in the present invent:ion may oe produced by a method which i5 basically the same as the one described in Japanese Patent Publication No. 1~560~67. The method comprises the step in which a mixture- o an unsintered ~TF~ powder and a liquid lubricant is supplied into a ram ex.ruder to extrude in a tubular form, the tube thus obtained is then stretched in the axial direction, with radial expansion being optionally achieved simultaneously or afterward, while the liquid lubricant is or is not removed from the tube; thereafter while the stretched tube is fixed to prevent shrinkage, the stretched tube is sintered by heating to a sintering temperature of 327C ox more to fix the stretched structure.
Examples of the liquid lublicant used in the present invention include those described in Japanese 1 Patent Publication No. 13560/67.
The resulting PTFE porous tube provided with increased strength has a microfibrous structure comprising small nodes interconnected with many thin fibrils. The diameter and length of the fibrils and the size and number of the nodes can be varied by changing the conditions of stretching and sintering operations, and thus the pore size and porosity of ~he porous tube thus obtained can be freely controlled. It has been clinically reported that when this type of porous tube i~ used as an artificial blood vessel, it preferably has an average pore size of from 1 to LOO micrometers, a porosi~y of 70% or more, and a tube wall thickness of from 0.3 to 1.0 mm.
The PTFE porous tube prodused by the method described a~ove is typically characte~izea in that the fibrous structure of PT~E is predominan ly oriented in the - axial direction. In accordance with the present invention, the stretched tube is sintered, while being fixed to prevent thermal shrinkage, by heating the outer surface of the tube to a temperature of 327C or higher until it acquires a meshed or network-like structure. By this process, the outer surface of the tube attains a larger 2verase pore size than the inner surface and the fibrous structure of PTFE is caused to vary continuously across the wall thickness from the inner surface which is predominantly oriented along the axial direction to the g _ ;
;
2~i~7 1 outer surface which is predominantly oriented along the concentric direction. The present invention offers this PTFE porous tube as a tubular prosthesis.
The outer surface of the tube is provided with a meshed or network-like structure by heating the tube from outside to a temperature of 327C or higher. As the tube is heated to such elevated temperature, the fibrils in the outer surfac~! of the PTFE tube increase in diameter because of t~e cutting or coalescing of the microfibrils and the coalescins of the nodes. This causes a corresponding increase in the pore size, or the diameter of the gap between adjacent fibrils~ The higher the temperature at which the outer surface of the tube is maint~ined and the longer the period auring which it is maintained a~ temperatures higher than 327C, the more pronouncedly l:he phenomenon described above occur, and the outer surface of the tube will eventually attain a network-like structure having pore sizes of from several tens micrometers to several millimeters. This change in ibrous structure will proceed into the tube wall, provides a smooth ,pore size gradient through the wall thickness from the inner surface to the outer surface.
The fibrous structure of the outer surface of the PT~E
porous tube thus produced is highly oriented 'along the concentric direction, and is transverse to the axial direction along which the fibril structure of the tube has -- 10 ~
5~
1 been oriented as a result of the stretching.
As described above, by appropriately controlling the temperature and time conditions to be employed for sintering operations, the PTFE tube can be provided with a s gradual profile of change in its fibrous structure through the thickness of the tube wall wherein the porous structure of the inner surfce is predominantly oriented alon~ the axial direction and that of tne outside surface is highly oriented along the concentric dlrection. One characteristic of the present in~ention is to allow the stretched PTFE tube to be sinteLed to a far greater extent than has been achieved with the conventional PT E sinters.
The tublar prosthesis of the present invention preerably has an average fibril lengtn of the outer surface thereof which is at least ~ times, more preferably at least 10 times, that of the inner surface. The thickness of the nodes in the outer surface of the tublar prosthesis of the present invention is preferably at least 10 times that of the inner suraface.
In order for the tubular prosthesis of the present invention to be used as an artificial blood vessel, the average pore sizes in the inner and outer surfaces of the PTFE porous tube are preferably within the ranges of from 1 to 100 micrometers and fLom 0.1 to 1.0 mm, respectively, and these pore size ranges could be easily attained by the present invention. The tubular 125~S~3~
1 prosthesis of the present invention is possessed of such improved characteristics that it is highly resistant to tearing and buckling. In addition, the prosthesis has an improved ability to bind with the tissues of a living body because of the presence of the pores which provide passages for the penetration of the surrounding tissues.
The porosity of the ~TFE porous tube used in the present inven_ion is preferably from 70 to 90~, more preferàbly fro~ 75 to 85%.
O~her materials of ~he tubular prosthesis of the present invention wh;ch can be absorbed by a living body are described below.
Collagen is presen' in an amount of about 25 wt~
in skins, hides, tendons, bones, and soft bones of the animal body. Collagen is also present in the blood vessels and heart of an anima~ in amounts of from 5 to 10 wt~. Collagen is obtained by first decomposing the fa, tissues of calf s'~in with an appropriate enzyme such as lipase, then digesting the antigenic polypeptide portion with an appropriate enzyme such as pepsin. The temperature is critical to these procedures since if soluble collagen obtained is heated to a temperature higher than the melting point, which is between 4QC and 50C, it is converted to gelatin as a result of breakdown of the triple-stranded helical conformation of the three polypeptide strands in collagen. However, even the - ~2 -9XS~7 l gelatin formed as a re~ult of thermal denaturation has some capabilities s;milar to those of collagen, so that partially gelatinized collagen can be employedc Lt should however be emphasized that collagen without thermal denaturation i; particularly preferred.
Albumin is made of globular proteins present in the plasma component of the blood in a concentration of as high as 4 to 5 g/dl. Albumin serves to maintain the osmoti~ pressure of the blood and to transport various substances in the ~lood. Being ~ighly soluble in water, albumin is selectively adsorbed on hydrophilic sites of high molecular weight subs~ances which are in contact with the blood, anc this~ mây be com~a.e~ with the fact that ~-globulins relcting to immune reac~ions are insoluble in water and are adsorbed on hydrophobic sites of the blood-conta^ting hlg~ molecular w_ight subs~ances.
Hepa~in i5 present in liver, lung, intestines and skin, and is a polysaccharide wherein hydroxy groups in the cellu~ose structure are substituted by amino-suifate groups or sulate este~s. Heparin is known to bethe most potent anticoagulant.
Chitosan is made from chitin which is derived from the exoskeletons of insècts and crustaceans, and a par. of the hydroxy groups in the cellulose structure thereof is substituted by acetamido groups. Chitosan is made by deacetylating the acetamido groups in chitin with 1 alkali and is characterized by the presence of primary amino groups.
- The composite structure conternplated by the present invention may be attained by, for example, the following procedures. First, a fibrous structure of YTFE
in a tubular form having a predetermined inner diameter is submerged in an aqueous solution of albumin and dried under reduced pressure. Subsequently, the tube is submerged in an aqueous solution of colla~en and dried under reduced pressure. The outer surface of the tube is then applied with a collagen solution and dried. The inner surface of the tube is subsequently applied with a mixed solutior of albumin and heparin and dried at room temperature. The biopolymers in the resulting composite structure, that is albumin, collagen, and heparin, are crosslinked by the treatment with an aqueous solution of a dialdehyde compound (e.g., glutaraldehyde, dialdehyde starch, glyoxal, etc.) so that they becomes water-insoluble.
Another method for attaining the composite structure starts with a fibrous structure of PTFE in a tubular form having a predetermined inside diameter which is submerged in an aqueous solution of chitosan and dried under reduced pressure; then the tube is submerged in an aqueous solution of collagen and dried under reduced pressure; the outer surface of the tube is applied with a "~' ,. ~ ....
32~7 1 collagen solution and dried; the inner surface of the tube is subsequently applied with a mixed solution of chitosan and heparin and dried at room temperature. As in the first method, the biopolymers in the resulting composite structure, that is chitosan, collagen, and heparin, are crosslinked by treatment wi~h an aqueous solution of a dialdehyde ccmpound (e.g., glutaraldehyde, dialdehyde starch, glyoxal, etc.~ so that they becomes insoluble in water.
The process for pr~ducing the composite structure of the present invention allows for a fairly large latituae in selecting the order of applying and impregnating the biopolymers so long 2S the intended laminar structure is impa~ted to the wall of the PTFE
tube. For instance, the PTFE tube is first impregnated with a mixed solution of albumin and/or chitosan and collagen, then applied on the inner surface with albumin and/or chitosanl followed by heparin applying, and finally the outer surEace of the tube is applied with collagen.
In another approach, the tube is first impregnated with a solution of albumin and/or chitosan, applied on the outer surface with collagen, and finally applied on the inner surface with heparin. The biopolymers may be impregnated or applied by impregnation under vacuum or injection under pressure.
The biopolymers may be acidic or alkaline, in .
.
-~Z~:5~7 1 order to attain higher solubilities to water or physiological saline solution~ The solutions of biopolymers generally have concentra~ions within the range of from 0.05 to 10 wt% but collagen may be dissolved at a concentration of as high as 20 wt~. In order to permit the biopolymers to be uniformly impregnated in the bulk oE
the fibrous sl:ructure of PT~E or to be applied uniformly on its surface/ it is preerred that the PTFE tube be first washed ~7ith an a?propriate solvent such as alcohol, then washed with water and impregnated with the biopolymers at a concentration of from 0.1 to 5 wt~. The duration of t:he pericc during which the PTFE tube is subme~ged in biopolymer solutions may range from 1 to 10 minut~s but, if the fibrous structure OL- PTF3 is c~pr2ssed with an appropriate means such as rollers, the pe_iod can be reduced to less than 1 minute without sacrificing he uniformity o, impregnation OL the biopolymers. The applied biopolymers may be adequately crosslinked by submerging the tube within an aqueous solution of a dialdehyde compound having a concentration o from 0.05 to 0.5%, preferably from 0.2 to 0.5%, for a perioa of from 1 minute to 48 hours.
While, as discussed above, the tubular prosthesis of the present inven~ion is highly useful as an artificial blood vessel, it is also useful as a replacement for other tubular organs such as the `' ` :1~29Z597 1 esophagus, tracchea, bile duct, ureter and urethra.
The following examples are provided for the purpose of further illustrating the advantages of the present invention but are in no way to be taken as limiting the scope of the invention. Unless otherwise indicated, all parts, ratios, and percents are by weight.
EXAMPLE I
Preparation of poros PTFE tube A hundred parts by weight of a fine PTFE powder .,..
t~olyflon F-104E produced by Daikin Kogyo Co., Ltd.) was intima~ely mixed with 29 parts by weight of a liquid lubricant (DO';3 produced by Shell Chemical Co., ~td., containing 99.98 vol~ of paraffin). The mixture was shaped into 2! preEorm, and then supplied into a ram extruder ~o extrude a tubular form having an inner - diameter of 3.0 mm and an outer diameter o 4.5 mm. The tube thus-obtained was submerged in trichloroethylene to extract the liquid lubricant. The tube was stretched 300%
in the axial clirection while being heated at about 250C.
The thus-stret:ched tube was heated at about 330C and inflated by appl~ing vacuum onto the outer surface thereof so as to make the porous PTFE tube having an inner diameter of 4.0 mm. A stainless steel rod with a diameter of 4.0 mm was inserted through the tube, and then the tube was heated at 350C for 30 minutes with both ends fixed to the rod. After being cooled to room temperature, the r~d~
` ~Z~5~'7 1 steel rod was withdrawn from ~che tube which had assumed an inner diameter of 4.0 mm, an outer diameter of ~.9 mm, a porosity of 80%, and average pore sizes of 2.0 micrometers and 0.15 mm on the inner and outer surfaces, respectively.
A stainless steel wire having a diameter of 0.4 mm was pierced through the tube wall at a distance of 5 mm from one end of the tube and both ends of the wire were joined to form a loop. When the loop was pulled along the axial direction at a rate of 50 mm/min, the tube did not tear until the :load increased to 3,800 g, which was significantly greater than 180 g correspond the tear strength of a PTFE porous tube prepared by the conventional sintering method. Because af this remarkable improvement in tear strength, the tube could be sutured with blood vessels in a host body with little chance o-tearing in the longidutinal direction.
Preparation of Collagen Solution Calf skin was broken into small pieces and mixea with HCl to attain a pH of 3. About 1 wt% of pepsin based on the amount of collagen contained in the calf skin was added to the mixture and agitated for 4 to 5 days at room temperature. The viscous collagen solution thus-obtained was neutralized with NaOH to attain a pH of 7 to 8, whereupon a collagen precipitate formed. The precipitated collagen was collected by centrifugation, washed with 5~7 1 water and dissolved in 0.5 M NaC1 in a concentration of 0.5 wt~.
E~AMPLE 3 Preparation of Albumin Solution Human serum albumin was dissolved in a 0.2 M
phosphate buffer (pH: 7.4) for a concentration of 0~3 wt%.
In order to achieve uniform impregnation in the hydrophobic PTFE porous tube, the albumin solution was placed in a capillary equiped with a cock connected to a vacuum line. The capi~lary was a'lso equiped at the bottom with a cock for providing a pass2ge ~hroush whlch t.he albumin solution could be dischar~ed and the phosphate buffer introduced. ~ , -~ EX~MPLE
PreParation of Chitosan Solution A c~ab shell was broken into srnall pieces and agitated in .! N HCl for 3 days to extract the soluble -components. The insoluble components were heated with agitation in l N NaOH to extract any residual soluble components. The insoluble components were dried and heated to 180C under nitrogen in the presence of 5 times volume of NaOH. Alkali fusion occurred and thus chitin was deacetylated to produce chitosan. The preci?itate was washed with water and dissolved in a 1~ acetic acid solution for a chitosan concentration of 1.2 wt~.
Z~
Pre~aration of Mixed Solution of Collagen and Albumin The collagen solution prepared in Example 2 and the albumin solution prepared in Example 3 ~7ere slowly mixed at a temperature not higher than 5C. Any fibrous precipitae forming in a trace amount was dissolved by the addition of 0.05 N HCl~
Pre~araton o' l~ixed Solution of Collagen and Chitosan The collasen solution prepared in Example 2 and the chitosan ,olutior. prepared in Example 4 were slowly mixed at a tenperature not higher than 5~C. Any fibrous precipitate forming in a trace amount was dissolved by the ! adcition of 0.1 N ~Clo E~MPLE 7 Pre?aration of Mixed Solution Oc ~lbu~ln and Heparin To the albur~.in solution prepared in Example 3, heparin sodiur~ salt as dlssolved in -a 0.2 M phosphate buffer (pH: 7) was added dropwise so as to form a solution wherein the amino groups in albumin were ionically bound to the s~lfate groups in heparin.
Pr~aration of_Mixed Solution of Chitosan and Heparin To the chitosan solution prepared in Example 4 r heparin sodium salt as dissolved in a 0.2 M phosphate buffer (pH: 7) was added dropwise so as to Eorm a solution l wherein the amino groups in chitosan were ionically bound to the sulfate groups in heparin.
Application onto the Inner Surface of PTFE Tube The porous PTFE tube prepared in Example 1 was submerged in the mixed solution prepared in Example 5. In order to allow the solution to be uniformly impregnated in the porous structure of the PTFE tube, the tube was subjected to ~t least three cycles of evacuation and pressurization while it was immobilized in the solution.
Thereafter, the tube was left to stand at 20C for 12 hours. After the mixed solution was discharged, the tu~e was .:dried und_r reduced pressure at room temperature r was~ed with 0.02 N NaOH, then with a 0.2 M phosphate bufferO
E~PLE 10 Application onto the Outer Surface of PTFE Tube The outer surface of the PTFE porous tube prepared in Example 9 was applied with the collagen solution prepared in Example 2. The tube was thereafter dried under reduced pressure and then washed with distilled water.
Better results are attained ;.n Examples 9 and 10 if the treatments of the PTFE porous tube are conducted with a stainess steel rod being inserted through the tube as in Example l. The two particular advantages resulting ~zs~
1 from the use of a stainless steel rod are (i) a PTFE tube having a small specific gravity can be immobilized in the biopolymer solution even if the interior of the tube is maintained under vacuum; and (ii) uniform application can s be conducted to the outer surface of the tube by applying the collagen solution over a given period whlle rotating the stainless steel rod with the both ends thereof being fixed.
Applica~ion onto the Inner Surface or PTF~ tube and Crossl~n'cinG with Dialdehyde The mxied solution of albumin and heparin prepared in E~tample 7 was applied onto the inner surface of the PmFE porous tube prepared in Example 10~ Before the applic~ion, the stainless steel rod had been withdrawn f-om the PTFE tube. ~ syringe charged with the mixed solution of albumin and heparin w~s connected to t'r.e PTFE tube and the solution was introduced at 20C for a period of 2 to 20 hours (preferably 5 hours) such that it would contact only the inside surface of the tube.
Thereafter, the tube was submerged within a 0.3%
dialdehyde starch solution at 25C for 20 minutes, and dried under reduced pressure.
Application onto the Inner Surface o~ PTFE Tube The porous PTFE tube prepared in Example 1 was z~
1 submerged in the mixed solution prepared in Example 6. In order to allow the solution to be uniformly impregnated in the porous structure of the PTFE tube, the tube was subjected to at least three cycles of evacuation and pressurization at 20C while immobilized in the solution.
Thereafter, the mixed solution was discharyed and the tube was dried under reduced pressure at room temperature, washed first w..th 0.1 ~ NaOH, then with distilled water.
A~plication onl:o the Outer Surfaceïof PTFE Tu'?e The ~ute sur.ace of the PTFE tube prepared in Example 12 was applied with the collagen solution prepared in Examp'e 2 at 20C or 1 hour. ~he tube was .hereafter dried under reduced pressure and washed with distilled water. For the same reasons as glven in conne~tion with Examples 9 and 10, be.ter results are attained in Examples 12 and 13 by treating the PTFE tube with a stainless steel rod being inserted through the tube.
Application OlltO the Inner Surface of PTFE Tube and Crosslinkin~ with Glutaraldehyde The mixed solution of Ghitosan and heparin prepared in Example 8 was applied onto the inne~ surface o the PTFE porous tube prepared in Example 13. Before the application, a stainless steel rod had been withdrawn from the PTFE tube. A syringe charged with the mixed ~Z9Z~i97 1 solution of chitosan and heparin was connected to the PTFE
tube and the solution was introduced at 20C for a period of 2 to 20 hours (preferably 5 hours) such that it would contact only the inner surface of the tube. Thereafter, the tube was submerged within a 0.16 glutaraldehyde solution at 25C for 10 hours, and dried under reduced pressure.
EX~MPLE 15 A porous PTFE tube was prepared in the same manner as in Example 1 except that the unsintered PTFE
tube havins an inner diameter of 2.0 mm was expanded to 3.0 mm bv sintering, By the same manner as in Examples 9 to 11, a ~ubular prosthesis having an inside diameter of . 3.0 mm was fabricated.
E~MPLE 16 The PTF~ tube prepared in Example 1 was submerged in a 2~ aqueous solution of poly~oxyethylene nonylphenyl et:her) and subsequently dried. The tube was submerged in the~ solution prepared in Example 3, and dried thereafter. The outer surface of the tube was applied with the solution prepared in Example ~. After withdrawing the stainless steel rod from the tube, the solution prepared in Example 7 was supplied onto only th~
inner sur~ace thereof, which was thereafter washed with a phosphate buffer. The tube was subjected to crosslinking by submerging withln a 0.2~ aqueous solution of 1 glutaraldehyde at 25C for 8 hours, and finally washed with a phosphate buffer.
The PTFE tubes prepared in Examples 11, 14, 15 and 16 were found to have superior characteristics that made them highly suitable for use as artificial blood vessels.
While the invention has been described in detail and with reference to specific examples thereo~, it will be apparent to one s~illed in the art that various chan~es and modifications can be made therein without departing from the spiril and scope thereof.
The outer surface of the tube is provided with a meshed or network-like structure by heating the tube from outside to a temperature of 327C or higher. As the tube is heated to such elevated temperature, the fibrils in the outer surfac~! of the PTFE tube increase in diameter because of t~e cutting or coalescing of the microfibrils and the coalescins of the nodes. This causes a corresponding increase in the pore size, or the diameter of the gap between adjacent fibrils~ The higher the temperature at which the outer surface of the tube is maint~ined and the longer the period auring which it is maintained a~ temperatures higher than 327C, the more pronouncedly l:he phenomenon described above occur, and the outer surface of the tube will eventually attain a network-like structure having pore sizes of from several tens micrometers to several millimeters. This change in ibrous structure will proceed into the tube wall, provides a smooth ,pore size gradient through the wall thickness from the inner surface to the outer surface.
The fibrous structure of the outer surface of the PT~E
porous tube thus produced is highly oriented 'along the concentric direction, and is transverse to the axial direction along which the fibril structure of the tube has -- 10 ~
5~
1 been oriented as a result of the stretching.
As described above, by appropriately controlling the temperature and time conditions to be employed for sintering operations, the PTFE tube can be provided with a s gradual profile of change in its fibrous structure through the thickness of the tube wall wherein the porous structure of the inner surfce is predominantly oriented alon~ the axial direction and that of tne outside surface is highly oriented along the concentric dlrection. One characteristic of the present in~ention is to allow the stretched PTFE tube to be sinteLed to a far greater extent than has been achieved with the conventional PT E sinters.
The tublar prosthesis of the present invention preerably has an average fibril lengtn of the outer surface thereof which is at least ~ times, more preferably at least 10 times, that of the inner surface. The thickness of the nodes in the outer surface of the tublar prosthesis of the present invention is preferably at least 10 times that of the inner suraface.
In order for the tubular prosthesis of the present invention to be used as an artificial blood vessel, the average pore sizes in the inner and outer surfaces of the PTFE porous tube are preferably within the ranges of from 1 to 100 micrometers and fLom 0.1 to 1.0 mm, respectively, and these pore size ranges could be easily attained by the present invention. The tubular 125~S~3~
1 prosthesis of the present invention is possessed of such improved characteristics that it is highly resistant to tearing and buckling. In addition, the prosthesis has an improved ability to bind with the tissues of a living body because of the presence of the pores which provide passages for the penetration of the surrounding tissues.
The porosity of the ~TFE porous tube used in the present inven_ion is preferably from 70 to 90~, more preferàbly fro~ 75 to 85%.
O~her materials of ~he tubular prosthesis of the present invention wh;ch can be absorbed by a living body are described below.
Collagen is presen' in an amount of about 25 wt~
in skins, hides, tendons, bones, and soft bones of the animal body. Collagen is also present in the blood vessels and heart of an anima~ in amounts of from 5 to 10 wt~. Collagen is obtained by first decomposing the fa, tissues of calf s'~in with an appropriate enzyme such as lipase, then digesting the antigenic polypeptide portion with an appropriate enzyme such as pepsin. The temperature is critical to these procedures since if soluble collagen obtained is heated to a temperature higher than the melting point, which is between 4QC and 50C, it is converted to gelatin as a result of breakdown of the triple-stranded helical conformation of the three polypeptide strands in collagen. However, even the - ~2 -9XS~7 l gelatin formed as a re~ult of thermal denaturation has some capabilities s;milar to those of collagen, so that partially gelatinized collagen can be employedc Lt should however be emphasized that collagen without thermal denaturation i; particularly preferred.
Albumin is made of globular proteins present in the plasma component of the blood in a concentration of as high as 4 to 5 g/dl. Albumin serves to maintain the osmoti~ pressure of the blood and to transport various substances in the ~lood. Being ~ighly soluble in water, albumin is selectively adsorbed on hydrophilic sites of high molecular weight subs~ances which are in contact with the blood, anc this~ mây be com~a.e~ with the fact that ~-globulins relcting to immune reac~ions are insoluble in water and are adsorbed on hydrophobic sites of the blood-conta^ting hlg~ molecular w_ight subs~ances.
Hepa~in i5 present in liver, lung, intestines and skin, and is a polysaccharide wherein hydroxy groups in the cellu~ose structure are substituted by amino-suifate groups or sulate este~s. Heparin is known to bethe most potent anticoagulant.
Chitosan is made from chitin which is derived from the exoskeletons of insècts and crustaceans, and a par. of the hydroxy groups in the cellulose structure thereof is substituted by acetamido groups. Chitosan is made by deacetylating the acetamido groups in chitin with 1 alkali and is characterized by the presence of primary amino groups.
- The composite structure conternplated by the present invention may be attained by, for example, the following procedures. First, a fibrous structure of YTFE
in a tubular form having a predetermined inner diameter is submerged in an aqueous solution of albumin and dried under reduced pressure. Subsequently, the tube is submerged in an aqueous solution of colla~en and dried under reduced pressure. The outer surface of the tube is then applied with a collagen solution and dried. The inner surface of the tube is subsequently applied with a mixed solutior of albumin and heparin and dried at room temperature. The biopolymers in the resulting composite structure, that is albumin, collagen, and heparin, are crosslinked by the treatment with an aqueous solution of a dialdehyde compound (e.g., glutaraldehyde, dialdehyde starch, glyoxal, etc.) so that they becomes water-insoluble.
Another method for attaining the composite structure starts with a fibrous structure of PTFE in a tubular form having a predetermined inside diameter which is submerged in an aqueous solution of chitosan and dried under reduced pressure; then the tube is submerged in an aqueous solution of collagen and dried under reduced pressure; the outer surface of the tube is applied with a "~' ,. ~ ....
32~7 1 collagen solution and dried; the inner surface of the tube is subsequently applied with a mixed solution of chitosan and heparin and dried at room temperature. As in the first method, the biopolymers in the resulting composite structure, that is chitosan, collagen, and heparin, are crosslinked by treatment wi~h an aqueous solution of a dialdehyde ccmpound (e.g., glutaraldehyde, dialdehyde starch, glyoxal, etc.~ so that they becomes insoluble in water.
The process for pr~ducing the composite structure of the present invention allows for a fairly large latituae in selecting the order of applying and impregnating the biopolymers so long 2S the intended laminar structure is impa~ted to the wall of the PTFE
tube. For instance, the PTFE tube is first impregnated with a mixed solution of albumin and/or chitosan and collagen, then applied on the inner surface with albumin and/or chitosanl followed by heparin applying, and finally the outer surEace of the tube is applied with collagen.
In another approach, the tube is first impregnated with a solution of albumin and/or chitosan, applied on the outer surface with collagen, and finally applied on the inner surface with heparin. The biopolymers may be impregnated or applied by impregnation under vacuum or injection under pressure.
The biopolymers may be acidic or alkaline, in .
.
-~Z~:5~7 1 order to attain higher solubilities to water or physiological saline solution~ The solutions of biopolymers generally have concentra~ions within the range of from 0.05 to 10 wt% but collagen may be dissolved at a concentration of as high as 20 wt~. In order to permit the biopolymers to be uniformly impregnated in the bulk oE
the fibrous sl:ructure of PT~E or to be applied uniformly on its surface/ it is preerred that the PTFE tube be first washed ~7ith an a?propriate solvent such as alcohol, then washed with water and impregnated with the biopolymers at a concentration of from 0.1 to 5 wt~. The duration of t:he pericc during which the PTFE tube is subme~ged in biopolymer solutions may range from 1 to 10 minut~s but, if the fibrous structure OL- PTF3 is c~pr2ssed with an appropriate means such as rollers, the pe_iod can be reduced to less than 1 minute without sacrificing he uniformity o, impregnation OL the biopolymers. The applied biopolymers may be adequately crosslinked by submerging the tube within an aqueous solution of a dialdehyde compound having a concentration o from 0.05 to 0.5%, preferably from 0.2 to 0.5%, for a perioa of from 1 minute to 48 hours.
While, as discussed above, the tubular prosthesis of the present inven~ion is highly useful as an artificial blood vessel, it is also useful as a replacement for other tubular organs such as the `' ` :1~29Z597 1 esophagus, tracchea, bile duct, ureter and urethra.
The following examples are provided for the purpose of further illustrating the advantages of the present invention but are in no way to be taken as limiting the scope of the invention. Unless otherwise indicated, all parts, ratios, and percents are by weight.
EXAMPLE I
Preparation of poros PTFE tube A hundred parts by weight of a fine PTFE powder .,..
t~olyflon F-104E produced by Daikin Kogyo Co., Ltd.) was intima~ely mixed with 29 parts by weight of a liquid lubricant (DO';3 produced by Shell Chemical Co., ~td., containing 99.98 vol~ of paraffin). The mixture was shaped into 2! preEorm, and then supplied into a ram extruder ~o extrude a tubular form having an inner - diameter of 3.0 mm and an outer diameter o 4.5 mm. The tube thus-obtained was submerged in trichloroethylene to extract the liquid lubricant. The tube was stretched 300%
in the axial clirection while being heated at about 250C.
The thus-stret:ched tube was heated at about 330C and inflated by appl~ing vacuum onto the outer surface thereof so as to make the porous PTFE tube having an inner diameter of 4.0 mm. A stainless steel rod with a diameter of 4.0 mm was inserted through the tube, and then the tube was heated at 350C for 30 minutes with both ends fixed to the rod. After being cooled to room temperature, the r~d~
` ~Z~5~'7 1 steel rod was withdrawn from ~che tube which had assumed an inner diameter of 4.0 mm, an outer diameter of ~.9 mm, a porosity of 80%, and average pore sizes of 2.0 micrometers and 0.15 mm on the inner and outer surfaces, respectively.
A stainless steel wire having a diameter of 0.4 mm was pierced through the tube wall at a distance of 5 mm from one end of the tube and both ends of the wire were joined to form a loop. When the loop was pulled along the axial direction at a rate of 50 mm/min, the tube did not tear until the :load increased to 3,800 g, which was significantly greater than 180 g correspond the tear strength of a PTFE porous tube prepared by the conventional sintering method. Because af this remarkable improvement in tear strength, the tube could be sutured with blood vessels in a host body with little chance o-tearing in the longidutinal direction.
Preparation of Collagen Solution Calf skin was broken into small pieces and mixea with HCl to attain a pH of 3. About 1 wt% of pepsin based on the amount of collagen contained in the calf skin was added to the mixture and agitated for 4 to 5 days at room temperature. The viscous collagen solution thus-obtained was neutralized with NaOH to attain a pH of 7 to 8, whereupon a collagen precipitate formed. The precipitated collagen was collected by centrifugation, washed with 5~7 1 water and dissolved in 0.5 M NaC1 in a concentration of 0.5 wt~.
E~AMPLE 3 Preparation of Albumin Solution Human serum albumin was dissolved in a 0.2 M
phosphate buffer (pH: 7.4) for a concentration of 0~3 wt%.
In order to achieve uniform impregnation in the hydrophobic PTFE porous tube, the albumin solution was placed in a capillary equiped with a cock connected to a vacuum line. The capi~lary was a'lso equiped at the bottom with a cock for providing a pass2ge ~hroush whlch t.he albumin solution could be dischar~ed and the phosphate buffer introduced. ~ , -~ EX~MPLE
PreParation of Chitosan Solution A c~ab shell was broken into srnall pieces and agitated in .! N HCl for 3 days to extract the soluble -components. The insoluble components were heated with agitation in l N NaOH to extract any residual soluble components. The insoluble components were dried and heated to 180C under nitrogen in the presence of 5 times volume of NaOH. Alkali fusion occurred and thus chitin was deacetylated to produce chitosan. The preci?itate was washed with water and dissolved in a 1~ acetic acid solution for a chitosan concentration of 1.2 wt~.
Z~
Pre~aration of Mixed Solution of Collagen and Albumin The collagen solution prepared in Example 2 and the albumin solution prepared in Example 3 ~7ere slowly mixed at a temperature not higher than 5C. Any fibrous precipitae forming in a trace amount was dissolved by the addition of 0.05 N HCl~
Pre~araton o' l~ixed Solution of Collagen and Chitosan The collasen solution prepared in Example 2 and the chitosan ,olutior. prepared in Example 4 were slowly mixed at a tenperature not higher than 5~C. Any fibrous precipitate forming in a trace amount was dissolved by the ! adcition of 0.1 N ~Clo E~MPLE 7 Pre?aration of Mixed Solution Oc ~lbu~ln and Heparin To the albur~.in solution prepared in Example 3, heparin sodiur~ salt as dlssolved in -a 0.2 M phosphate buffer (pH: 7) was added dropwise so as to form a solution wherein the amino groups in albumin were ionically bound to the s~lfate groups in heparin.
Pr~aration of_Mixed Solution of Chitosan and Heparin To the chitosan solution prepared in Example 4 r heparin sodium salt as dissolved in a 0.2 M phosphate buffer (pH: 7) was added dropwise so as to Eorm a solution l wherein the amino groups in chitosan were ionically bound to the sulfate groups in heparin.
Application onto the Inner Surface of PTFE Tube The porous PTFE tube prepared in Example 1 was submerged in the mixed solution prepared in Example 5. In order to allow the solution to be uniformly impregnated in the porous structure of the PTFE tube, the tube was subjected to ~t least three cycles of evacuation and pressurization while it was immobilized in the solution.
Thereafter, the tube was left to stand at 20C for 12 hours. After the mixed solution was discharged, the tu~e was .:dried und_r reduced pressure at room temperature r was~ed with 0.02 N NaOH, then with a 0.2 M phosphate bufferO
E~PLE 10 Application onto the Outer Surface of PTFE Tube The outer surface of the PTFE porous tube prepared in Example 9 was applied with the collagen solution prepared in Example 2. The tube was thereafter dried under reduced pressure and then washed with distilled water.
Better results are attained ;.n Examples 9 and 10 if the treatments of the PTFE porous tube are conducted with a stainess steel rod being inserted through the tube as in Example l. The two particular advantages resulting ~zs~
1 from the use of a stainless steel rod are (i) a PTFE tube having a small specific gravity can be immobilized in the biopolymer solution even if the interior of the tube is maintained under vacuum; and (ii) uniform application can s be conducted to the outer surface of the tube by applying the collagen solution over a given period whlle rotating the stainless steel rod with the both ends thereof being fixed.
Applica~ion onto the Inner Surface or PTF~ tube and Crossl~n'cinG with Dialdehyde The mxied solution of albumin and heparin prepared in E~tample 7 was applied onto the inner surface of the PmFE porous tube prepared in Example 10~ Before the applic~ion, the stainless steel rod had been withdrawn f-om the PTFE tube. ~ syringe charged with the mixed solution of albumin and heparin w~s connected to t'r.e PTFE tube and the solution was introduced at 20C for a period of 2 to 20 hours (preferably 5 hours) such that it would contact only the inside surface of the tube.
Thereafter, the tube was submerged within a 0.3%
dialdehyde starch solution at 25C for 20 minutes, and dried under reduced pressure.
Application onto the Inner Surface o~ PTFE Tube The porous PTFE tube prepared in Example 1 was z~
1 submerged in the mixed solution prepared in Example 6. In order to allow the solution to be uniformly impregnated in the porous structure of the PTFE tube, the tube was subjected to at least three cycles of evacuation and pressurization at 20C while immobilized in the solution.
Thereafter, the mixed solution was discharyed and the tube was dried under reduced pressure at room temperature, washed first w..th 0.1 ~ NaOH, then with distilled water.
A~plication onl:o the Outer Surfaceïof PTFE Tu'?e The ~ute sur.ace of the PTFE tube prepared in Example 12 was applied with the collagen solution prepared in Examp'e 2 at 20C or 1 hour. ~he tube was .hereafter dried under reduced pressure and washed with distilled water. For the same reasons as glven in conne~tion with Examples 9 and 10, be.ter results are attained in Examples 12 and 13 by treating the PTFE tube with a stainless steel rod being inserted through the tube.
Application OlltO the Inner Surface of PTFE Tube and Crosslinkin~ with Glutaraldehyde The mixed solution of Ghitosan and heparin prepared in Example 8 was applied onto the inne~ surface o the PTFE porous tube prepared in Example 13. Before the application, a stainless steel rod had been withdrawn from the PTFE tube. A syringe charged with the mixed ~Z9Z~i97 1 solution of chitosan and heparin was connected to the PTFE
tube and the solution was introduced at 20C for a period of 2 to 20 hours (preferably 5 hours) such that it would contact only the inner surface of the tube. Thereafter, the tube was submerged within a 0.16 glutaraldehyde solution at 25C for 10 hours, and dried under reduced pressure.
EX~MPLE 15 A porous PTFE tube was prepared in the same manner as in Example 1 except that the unsintered PTFE
tube havins an inner diameter of 2.0 mm was expanded to 3.0 mm bv sintering, By the same manner as in Examples 9 to 11, a ~ubular prosthesis having an inside diameter of . 3.0 mm was fabricated.
E~MPLE 16 The PTF~ tube prepared in Example 1 was submerged in a 2~ aqueous solution of poly~oxyethylene nonylphenyl et:her) and subsequently dried. The tube was submerged in the~ solution prepared in Example 3, and dried thereafter. The outer surface of the tube was applied with the solution prepared in Example ~. After withdrawing the stainless steel rod from the tube, the solution prepared in Example 7 was supplied onto only th~
inner sur~ace thereof, which was thereafter washed with a phosphate buffer. The tube was subjected to crosslinking by submerging withln a 0.2~ aqueous solution of 1 glutaraldehyde at 25C for 8 hours, and finally washed with a phosphate buffer.
The PTFE tubes prepared in Examples 11, 14, 15 and 16 were found to have superior characteristics that made them highly suitable for use as artificial blood vessels.
While the invention has been described in detail and with reference to specific examples thereo~, it will be apparent to one s~illed in the art that various chan~es and modifications can be made therein without departing from the spiril and scope thereof.
Claims (11)
1. A tubular prosthesis having a composite structure comprising (i) tubular polytetrafluoroethylene having a microfibrous structure comprising small nodes interconnected with fibrils and (ii) materials which can be absorbed by a living body wherein (a) said polytetrafluoroethylene has a greater average fibril length on the outer surface than on the inner surface, and the fibrous structure of said polytetrafluoroethelene varies continuously across the thickness of the tube wall wherein said inner surface has said fibrous structure being predominantly oriented along the axial direction and said outer surface has said fibrous structure being predominantly oriented along the concentric direction; and (b) said materials which can be absorbed by â living body are collagen, at least one of albumin and chitosan, and heparin, and are distributed in such a manner that collagen is present in the portion of the tube wall which is closest to the outer surface thereof while at least one of albumin and chitosan is present in the portion of the tube wall which is closest to the inner surface thereof, and heparin is present in the inner surface of the tube wall.
2. A tubular prosthesis having a composite structure as in claim 1, wherein the outer surface of said tubular polytetrafluoroethylene has an average fibril length which is at least 5 times that of the inner surface.
3. A tubular prosthesis having a composite structure as-in claim 2, wherein the outer surface of said tubular polytetrafluoroethylene has an average fibril length which is at least 10 times that of the inner surface.
4. A tubular prosthesis having a composite structure as in claim 1, wherein the nodes in the outer surface of said tublar polytetrafluoroethylene have a thickness which is at least 10 times that of nodes in the inner surface.
5. A tubular prosthesis having a composite structure as in claim 1, wherein said collagen has been freed of any antigenic groups by the treatment with pepsin and has been crosslinked with glutaraldehyde or dialdehyle starch.
6. A tubular prosthesis having a composite structure as in claim 1, wherein said chitosan is made by the partial acetylation with alkali of chitin and has been crosslinked with glutaraldehyde or dialdehyde starch.
7. A tubular prosthesis having a composite structure as in claim 1, wherein said tubular prosthesis has an inner diameter of 5 mm or less.
8. A tubular prosthesis having a composite structure as in claim 7, wherein said tubular prosthesis has an inner diameter of from 1 to 3 mm.
9. A tubular prosthesis having a composite structuer as in claim 1, wherein said tubular polytetrafluoroethylene has an average pore size in the inner surface thereof of from 1 to 100 micrometers and an average pore size in the outer surface thereof of from 0.1 to 1.0 mm.
10. A tublar prosthesis having a composite structure as in claim 1, wherein said tublar polytetrafluoroethylene has a porosity of from 70 to 90%.
11. A tublar prosthesis having a composite structure as in claim 10, wherein said tublar polytetrafluoroethylene has a porosity of from 75 to 80%.
Applications Claiming Priority (4)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP296492/85 | 1985-12-24 | ||
| JP60296491A JPH0732798B2 (en) | 1985-12-24 | 1985-12-24 | Composite structure tubular organ prosthesis |
| JP60296492A JPS62152469A (en) | 1985-12-24 | 1985-12-24 | Tubular organ prosthetic article having composite structure |
| JP296491/85 | 1985-12-24 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1292597C true CA1292597C (en) | 1991-12-03 |
Family
ID=26560700
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000525434A Expired - Lifetime CA1292597C (en) | 1985-12-24 | 1986-12-16 | Tubular prothesis having a composite structure |
Country Status (4)
| Country | Link |
|---|---|
| US (1) | US4822361A (en) |
| EP (1) | EP0230635B1 (en) |
| CA (1) | CA1292597C (en) |
| DE (1) | DE3683934D1 (en) |
Families Citing this family (73)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE3778195D1 (en) * | 1986-04-07 | 1992-05-21 | Agency Ind Science Techn | ANTITHROMOGENIC MATERIAL. |
| US5011494A (en) * | 1988-09-16 | 1991-04-30 | Clemson University | Soft tissue implant with micron-scale surface texture to optimize anchorage |
| US5219361A (en) * | 1988-09-16 | 1993-06-15 | Clemson University | Soft tissue implant with micron-scale surface texture to optimize anchorage |
| JP2678945B2 (en) * | 1989-04-17 | 1997-11-19 | 有限会社ナイセム | Artificial blood vessel, method for producing the same, and substrate for artificial blood vessel |
| US4990158A (en) * | 1989-05-10 | 1991-02-05 | United States Surgical Corporation | Synthetic semiabsorbable tubular prosthesis |
| US5147400A (en) * | 1989-05-10 | 1992-09-15 | United States Surgical Corporation | Connective tissue prosthesis |
| US5376118A (en) * | 1989-05-10 | 1994-12-27 | United States Surgical Corporation | Support material for cell impregnation |
| US5217495A (en) * | 1989-05-10 | 1993-06-08 | United States Surgical Corporation | Synthetic semiabsorbable composite yarn |
| US5098779A (en) * | 1990-06-25 | 1992-03-24 | W. L. Gore & Associates, Inc. | Carvable implant material |
| BR9106205A (en) * | 1990-10-31 | 1993-03-30 | Baxter Int | DEVICE FOR IMPLANTATION IN HOST, IMPLANTATION PROCESS, IMPLANTED DEVICE, AND IMMUNO INSULATION CONTAINER |
| US5632776A (en) * | 1990-11-22 | 1997-05-27 | Toray Industries, Inc. | Implantation materials |
| DE69229312T2 (en) * | 1991-03-29 | 1999-11-04 | Vascular Graft Research Center | ARTIFICIAL BLOOD VESSEL FROM COMPOSITE MATERIAL |
| US5500013A (en) * | 1991-10-04 | 1996-03-19 | Scimed Life Systems, Inc. | Biodegradable drug delivery vascular stent |
| US5584875A (en) * | 1991-12-20 | 1996-12-17 | C. R. Bard, Inc. | Method for making vascular grafts |
| DE69325649T2 (en) * | 1992-03-13 | 1999-11-18 | Atrium Medical Corp | OBJECTS OF EXPANDED FLUOROPOLYMER (e.g. POLYTETRAFLUORETHYLENE) WITH CONTROLLED POROSITY AND ITS PRODUCTION |
| US5354329A (en) * | 1992-04-17 | 1994-10-11 | Whalen Biomedical, Inc. | Vascular prosthesis having enhanced compatibility and compliance characteristics |
| US5383927A (en) * | 1992-05-07 | 1995-01-24 | Intervascular Inc. | Non-thromogenic vascular prosthesis |
| US5466509A (en) * | 1993-01-15 | 1995-11-14 | Impra, Inc. | Textured, porous, expanded PTFE |
| US5453235A (en) * | 1993-01-29 | 1995-09-26 | Impra, Inc. | Method of forming dual porosity FTFE tubes by extrusion of concentric preforms |
| JPH0767895A (en) * | 1993-06-25 | 1995-03-14 | Sumitomo Electric Ind Ltd | Antimicrobial artificial blood vessel and suture yarn for antimicrobial operation |
| US6159565A (en) * | 1993-08-18 | 2000-12-12 | W. L. Gore & Associates, Inc. | Thin-wall intraluminal graft |
| US6025044A (en) * | 1993-08-18 | 2000-02-15 | W. L. Gore & Associates, Inc. | Thin-wall polytetrafluoroethylene tube |
| US6027779A (en) * | 1993-08-18 | 2000-02-22 | W. L. Gore & Associates, Inc. | Thin-wall polytetrafluoroethylene tube |
| US5527353A (en) * | 1993-12-02 | 1996-06-18 | Meadox Medicals, Inc. | Implantable tubular prosthesis |
| US6334872B1 (en) | 1994-02-18 | 2002-01-01 | Organogenesis Inc. | Method for treating diseased or damaged organs |
| US7108826B2 (en) * | 1994-03-02 | 2006-09-19 | Boston Scientific Scimed, Inc. | High compliance, high strength catheter balloons useful for treatment of gastrointestinal lesions |
| ATE310839T1 (en) | 1994-04-29 | 2005-12-15 | Scimed Life Systems Inc | STENT WITH COLLAGEN |
| US5541304A (en) * | 1994-05-02 | 1996-07-30 | Hercules Incorporated | Crosslinked hydrogel compositions with improved mechanical performance |
| WO1995031945A1 (en) | 1994-05-19 | 1995-11-30 | Scimed Life Systems, Inc. | Improved tissue supporting devices |
| US5665114A (en) * | 1994-08-12 | 1997-09-09 | Meadox Medicals, Inc. | Tubular expanded polytetrafluoroethylene implantable prostheses |
| DE69524501T2 (en) * | 1994-08-12 | 2002-05-29 | Meadox Medicals Inc | Vascular graft impregnated with a heparin-containing collagen sealant |
| IL115321A (en) * | 1994-09-16 | 2000-08-31 | Univ Ramot | Thromboresistant surface treatment for biomaterials |
| US5578073A (en) * | 1994-09-16 | 1996-11-26 | Ramot Of Tel Aviv University | Thromboresistant surface treatment for biomaterials |
| US5782789A (en) * | 1994-10-19 | 1998-07-21 | Atrium Medical Corporation | Macrochannel phosthetic/delivery patch |
| US5709713A (en) * | 1995-03-31 | 1998-01-20 | Cardiovascular Concepts, Inc. | Radially expansible vascular prosthesis having reversible and other locking structures |
| US5733337A (en) * | 1995-04-07 | 1998-03-31 | Organogenesis, Inc. | Tissue repair fabric |
| US20020095218A1 (en) * | 1996-03-12 | 2002-07-18 | Carr Robert M. | Tissue repair fabric |
| US5725568A (en) * | 1995-06-27 | 1998-03-10 | Scimed Life Systems, Inc. | Method and device for recanalizing and grafting arteries |
| US5865723A (en) * | 1995-12-29 | 1999-02-02 | Ramus Medical Technologies | Method and apparatus for forming vascular prostheses |
| 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 |
| JP2001502605A (en) | 1996-01-30 | 2001-02-27 | メドトロニック，インコーポレーテッド | Articles and methods for making a stent |
| CA2197375C (en) * | 1996-02-15 | 2003-05-06 | Yasuhiro Okuda | Artificial blood vessel |
| US5607478A (en) * | 1996-03-14 | 1997-03-04 | Meadox Medicals Inc. | Yarn wrapped PTFE tubular prosthesis |
| US5851229A (en) * | 1996-09-13 | 1998-12-22 | Meadox Medicals, Inc. | Bioresorbable sealants for porous vascular grafts |
| US7749585B2 (en) * | 1996-10-08 | 2010-07-06 | Alan Zamore | Reduced profile medical balloon element |
| US6494904B1 (en) | 1996-12-27 | 2002-12-17 | Ramus Medical Technologies | Method and apparatus for forming vascular prostheses |
| US6077217A (en) * | 1997-06-25 | 2000-06-20 | Ramus Medical Technologies, Inc. | System and method for assembling graft structures |
| RU2128024C1 (en) * | 1997-08-07 | 1999-03-27 | Закрытое акционерное общество "Научно-производственный комплекс "Экофлон" | Implanted hollow prosthesis and method of its manufacture |
| US6316522B1 (en) | 1997-08-18 | 2001-11-13 | Scimed Life Systems, Inc. | Bioresorbable hydrogel compositions for implantable prostheses |
| US5854382A (en) * | 1997-08-18 | 1998-12-29 | Meadox Medicals, Inc. | Bioresorbable compositions for implantable prostheses |
| US6129757A (en) * | 1998-05-18 | 2000-10-10 | Scimed Life Systems | Implantable members for receiving therapeutically useful compositions |
| WO1999063051A2 (en) * | 1998-06-05 | 1999-12-09 | Organogenesis Inc. | Bioengineered flat sheet graft prostheses |
| ATE423577T1 (en) * | 1998-06-05 | 2009-03-15 | Organogenesis Inc | BIOLOGICALLY MODELED IMPLANTABLE PROSTHESES |
| MXPA00012063A (en) * | 1998-06-05 | 2003-04-22 | Organogenesis Inc | Bioengineered vascular graft support prostheses. |
| DE69940507D1 (en) * | 1998-06-05 | 2009-04-16 | Organogenesis Inc | BIOTECHNICALLY GENERATED VASCOPY THERAPY FOR IMPLANTATION |
| US6517571B1 (en) | 1999-01-22 | 2003-02-11 | Gore Enterprise Holdings, Inc. | Vascular graft with improved flow surfaces |
| AU770316B2 (en) * | 1999-05-18 | 2004-02-19 | Cryolife, Inc. | Self-supporting, shaped, three-dimensional biopolymeric materials and methods |
| US6921412B1 (en) | 1999-05-18 | 2005-07-26 | Cryolife, Inc. | Self-supporting, shaped, three-dimensional biopolymeric materials and methods |
| US6780497B1 (en) | 1999-08-05 | 2004-08-24 | Gore Enterprise Holdings, Inc. | Surface modified expanded polytetrafluoroethylene devices and methods of producing the same |
| US6521284B1 (en) | 1999-11-03 | 2003-02-18 | Scimed Life Systems, Inc. | Process for impregnating a porous material with a cross-linkable composition |
| US7220276B1 (en) * | 2000-03-06 | 2007-05-22 | Surmodics, Inc. | Endovascular graft coatings |
| CA2422852C (en) * | 2000-09-18 | 2012-06-26 | Organogenesis Inc. | Methods for treating a patient using a bioengineered flat sheet graft prostheses |
| US6770086B1 (en) * | 2000-11-02 | 2004-08-03 | Scimed Life Systems, Inc. | Stent covering formed of porous polytetraflouroethylene |
| AU2001297782B2 (en) * | 2000-11-07 | 2006-03-02 | Cryolife, Inc. | Expandable foam-like biomaterials and methods |
| DE10061936A1 (en) * | 2000-12-13 | 2002-07-04 | Valentin Kramer | Object from ePTFE and method of manufacturing the same |
| CA2483988C (en) * | 2002-05-02 | 2010-09-21 | Sumitomo Electric Industries, Ltd. | Expanded polytetrafluoroethylene products and process for their production |
| US7789908B2 (en) * | 2002-06-25 | 2010-09-07 | Boston Scientific Scimed, Inc. | Elastomerically impregnated ePTFE to enhance stretch and recovery properties for vascular grafts and coverings |
| US20060253190A1 (en) * | 2005-05-06 | 2006-11-09 | Kuo Michael D | Removeable stents |
| US20070250114A1 (en) * | 2006-04-20 | 2007-10-25 | Sdgi Holdings, Inc. | Flexible tissue sheath for fibrous connective tissue repair |
| KR20100046037A (en) * | 2007-08-31 | 2010-05-04 | 키토자임사 | Prosthesis for promoting the in vivo reconstruction of a hollow organ or a portion of a hollow organ |
| JP4996578B2 (en) * | 2008-10-28 | 2012-08-08 | 株式会社サンメディカル技術研究所 | Medical device or instrument comprising a porous structure |
| US9345486B2 (en) * | 2009-03-16 | 2016-05-24 | University Of Washington | Nanofibrous conduits for nerve regeneration |
Family Cites Families (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3276448A (en) * | 1962-12-14 | 1966-10-04 | Ethicon Inc | Collagen coated fabric prosthesis |
| CH472219A (en) * | 1963-06-15 | 1969-05-15 | Spofa Vereinigte Pharma Werke | Highly porous collagen tissue blood vessel prosthesis and method for producing the same |
| SE392582B (en) * | 1970-05-21 | 1977-04-04 | Gore & Ass | PROCEDURE FOR THE PREPARATION OF A POROST MATERIAL, BY EXPANDING AND STRETCHING A TETRAFLUORETENE POLYMER PREPARED IN AN PASTE-FORMING EXTENSION PROCEDURE |
| US4208745A (en) * | 1976-01-21 | 1980-06-24 | Sumitomo Electric Industries, Ltd. | Vascular prostheses composed of polytetrafluoroethylene and process for their production |
| US4234535A (en) * | 1976-04-29 | 1980-11-18 | Sumitomo Electric Industries, Ltd. | Process for producing porous polytetrafluoroethylene tubings |
| US4713070A (en) * | 1978-11-30 | 1987-12-15 | Sumitom Electric Industries, Ltd. | Porous structure of polytetrafluoroethylene and process for production thereof |
| DE2947743C2 (en) * | 1978-11-30 | 1983-12-08 | Sumitomo Electric Industries, Ltd., Osaka | Uniform, porous tubular structure made of polytetrafluoroethylene |
| US4378017A (en) * | 1980-03-21 | 1983-03-29 | Kureha Kagaku Kogyo Kabushiki Kaisha | Composite material of de-N-acetylated chitin and fibrous collagen |
| US4399123A (en) * | 1980-04-01 | 1983-08-16 | Oliver Roy F | Fibrous tissue dressing or implant |
| SU904693A1 (en) * | 1980-05-12 | 1982-02-15 | Первый Московский Ордена Ленина И Ордена Трудового Красного Знамени Медицинский Институт Им. И.М.Сеченова | Vessel prosthesis |
| US4326532A (en) * | 1980-10-06 | 1982-04-27 | Minnesota Mining And Manufacturing Company | Antithrombogenic articles |
| JPS58180162A (en) * | 1982-04-19 | 1983-10-21 | 株式会社高研 | Anti-thrombosis medical material |
| EP0589637B1 (en) * | 1992-09-21 | 1997-06-04 | Dow Corning Corporation | Improved electrorheological fluid formulations using organosiloxanes |
-
1986
- 1986-12-16 CA CA000525434A patent/CA1292597C/en not_active Expired - Lifetime
- 1986-12-22 EP EP86117854A patent/EP0230635B1/en not_active Expired - Lifetime
- 1986-12-22 DE DE8686117854T patent/DE3683934D1/en not_active Expired - Lifetime
- 1986-12-24 US US06/945,971 patent/US4822361A/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| EP0230635A2 (en) | 1987-08-05 |
| US4822361A (en) | 1989-04-18 |
| EP0230635B1 (en) | 1992-02-19 |
| EP0230635A3 (en) | 1988-04-06 |
| DE3683934D1 (en) | 1992-03-26 |
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