CA1220601A - Triaxially-braided fabric prosthesis - Google Patents
Triaxially-braided fabric prosthesisInfo
- Publication number
- CA1220601A CA1220601A CA000451068A CA451068A CA1220601A CA 1220601 A CA1220601 A CA 1220601A CA 000451068 A CA000451068 A CA 000451068A CA 451068 A CA451068 A CA 451068A CA 1220601 A CA1220601 A CA 1220601A
- Authority
- CA
- Canada
- Prior art keywords
- fibers
- prosthesis
- sets
- oriented
- longitudinal direction
- 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
- A61F2/08—Muscles; Tendons; Ligaments
-
- 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
- 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
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2412—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with soft flexible valve members, e.g. tissue valves shaped like natural valves
-
- 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
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2412—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with soft flexible valve members, e.g. tissue valves shaped like natural valves
- A61F2/2415—Manufacturing methods
-
- 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
-
- D—TEXTILES; PAPER
- D04—BRAIDING; LACE-MAKING; KNITTING; TRIMMINGS; NON-WOVEN FABRICS
- D04C—BRAIDING OR MANUFACTURE OF LACE, INCLUDING BOBBIN-NET OR CARBONISED LACE; BRAIDING MACHINES; BRAID; LACE
- D04C1/00—Braid or lace, e.g. pillow-lace; Processes for the manufacture thereof
- D04C1/06—Braid or lace serving particular purposes
-
- D—TEXTILES; PAPER
- D07—ROPES; CABLES OTHER THAN ELECTRIC
- D07B—ROPES OR CABLES IN GENERAL
- D07B1/00—Constructional features of ropes or cables
- D07B1/02—Ropes built-up from fibrous or filamentary material, e.g. of vegetable origin, of animal origin, regenerated cellulose, plastics
-
- 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
- A61F2240/00—Manufacturing or designing of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2240/001—Designing or manufacturing processes
- A61F2240/002—Designing or making customized prostheses
-
- 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
- A61L2430/00—Materials or treatment for tissue regeneration
- A61L2430/10—Materials or treatment for tissue regeneration for reconstruction of tendons or ligaments
-
- D—TEXTILES; PAPER
- D07—ROPES; CABLES OTHER THAN ELECTRIC
- D07B—ROPES OR CABLES IN GENERAL
- D07B2201/00—Ropes or cables
- D07B2201/10—Rope or cable structures
- D07B2201/1096—Rope or cable structures braided
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2401/00—Physical properties
- D10B2401/06—Load-responsive characteristics
- D10B2401/061—Load-responsive characteristics elastic
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2401/00—Physical properties
- D10B2401/06—Load-responsive characteristics
- D10B2401/063—Load-responsive characteristics high strength
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2403/00—Details of fabric structure established in the fabric forming process
- D10B2403/02—Cross-sectional features
- D10B2403/024—Fabric incorporating additional compounds
- D10B2403/0241—Fabric incorporating additional compounds enhancing mechanical properties
- D10B2403/02411—Fabric incorporating additional compounds enhancing mechanical properties with a single array of unbent yarn, e.g. unidirectional reinforcement fabrics
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2509/00—Medical; Hygiene
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2509/00—Medical; Hygiene
- D10B2509/06—Vascular grafts; stents
Abstract
TRTAXIALLY-BRAIDED FABRIC PROSTHESIS
Abstract A novel prosthesis for use in repairing or replacing soft tissue is disclosed, which comprises a triaxially-braided fabric element having interwoven first, second and third sets of fibers, with the fibers of the second and third sets being oriented at substantially the same acute braiding angle with respect to the fibers of the first set. An elongated ligament prosthesis exhibiting the desired properties of high strength and high elasticity may be prepared by selecting high elasticity fibers for the first set, orienting said first set of fibers in the longitudinal direction of the prosthesis and selecting fibers having high yield strength and high Young's modulus for the second and third sets.
A tubular prosthesis in which high elasticity fibers are oriented in the longitudinal direction is highly suitable for use as a vascular prosthesis. A pros-thesis of the invention may also be manufactured in the form of a prosthetic heart valve leaflet.
Abstract A novel prosthesis for use in repairing or replacing soft tissue is disclosed, which comprises a triaxially-braided fabric element having interwoven first, second and third sets of fibers, with the fibers of the second and third sets being oriented at substantially the same acute braiding angle with respect to the fibers of the first set. An elongated ligament prosthesis exhibiting the desired properties of high strength and high elasticity may be prepared by selecting high elasticity fibers for the first set, orienting said first set of fibers in the longitudinal direction of the prosthesis and selecting fibers having high yield strength and high Young's modulus for the second and third sets.
A tubular prosthesis in which high elasticity fibers are oriented in the longitudinal direction is highly suitable for use as a vascular prosthesis. A pros-thesis of the invention may also be manufactured in the form of a prosthetic heart valve leaflet.
Description
~æ~
TRIAXIhEEY~RhIDED FABRIC ~OSTHESIS
The na~ural ligaments are elongated bundles of collag-enous soft tissue that serve, amo~g other things, to hold the component bones of joints toge~her. The surgical treatment of diseased or damaged ligaments, e.g.
the anterior cruciate ligamen~, has been severely hampered bv the una~ailability of a suitable, generally accepted ligament prosthesis. The desired character-istics for a li~ament prosthesis include appropriate size and shape, biological compatibility, capability of being readily attached by the surgeon to the body of the patient, high fatigue resistance and mechanical behavior approximating that of the ligamentous tissue sought to be repaired or replaced.
The latter desired characteristic is particularly important. Natural ligaments are both strong and highly elastic, which qualities are generally not found together in a single material. Thus, for example, the anterior cruciate ligament of normal adult humans exhibits a yield point in ten~ion of about 50 kg. at a reversible elongation of about 28%, and a break point of about 60 kg~ (Typical adult human tendons are stronger and less elastic.) A number of ligam~nt and/or tendon pr~stheses are known in which the load bearing body portion is fabricated essentially of a single ~ynthetic material (see, e~ , U.S. Patents 3,176,316; 3,613,120;
4,127,g02; 4,149,277; 4,20g,859; 4,255,820; 4,329,743 and 4,345,339; U.K. ~atent 1,602,834 and European Published Patent Appln. 51,954). These monocomponent devices generally possess insufficient longitudinal elasticity and some also exhibit inadequate lcngitu-dinal break strength. As a result of their insufficient elasticity, this type of prosthesis must be forced into the region of plastic deformation to achieve the lonyitudinal elongation desired for normal anatomical function, e.g. flexion of a joint, which o course permanently impairs the mechanical function of the prosthesis.
~ ecently, ligament prostheses have been disclosed in U.S. Paten~s 4,246,660 and 4,301,551 in which the load bearing body portion is a bicomponent structure comprised of one material that imparts strength to the prosthesis and another ma~erial that imparts elasticity. The use of these prostheses alleviates the disadvantages described above for the monocomponent type of prosthesis.
However, the prostheses disclosed in the '660 and '551 Patents are complex in construction and their methods of attachment to the body of the patient involve rather complicated surgical procedures.
A recent thesis (Elizabe~h E. Fitzgerald, "Mechanical E,ehavior of Bicomponent Braids as Potential Surgical Implants", Master of Science Thesis, Cornell University, August 1979) has disclosed the use of a braided bicom-ponent tube as a ligament prosthesis. In this pros-thesis two interwoven sets of polymeric fibers, one of a strong material and the other of an elastic material, are helically-disposed in the wall of the tube and oriented at a fixed angle with respect to one another.
~6g~' Each set of fibers is oriented at the same acuke angle with respect to the longitudinal direction of the tube.
The prosthesis may additionally comprise a monocomponent polymeric filament core.
The prosthesis disclosed in the Fitzgerald thesis has certain inherent disadvantages. First, since the fibers in the two helically-disposed interwoven sets are not idential, the prosthesis is not balanced and will tend to twist during longitudinal elongation.
Second, since the set of helically-disposed elastic fibers is angulated with respect to the longitudinal direction of the prosthesis, only a minor amount of the work performed in elongating the prosthesis longi-tudinally is converted to elastic energy stored in the extended set of elastic fibers. Undesirably large portions of said work are converted to elastic energy stored in the other set of strong fibers or dissipated as ~riction in the extending trellis-like bicomponent braided structure.
It is an object of the present invention to provide a ligament prosthesis of simple construction that exhibits a yield strength in tension and a longitudinal elasticity that are a~ least comparable to that of a human ligament and a resistance to longitudinal elastic deformation in tension that approximates that of a human ligament.
Is ls another object of the invention to provide a balanced braided prosthesis of such construction that its longitudinal load-strain behavior can be readily "fine-t~ned", while maintaining balance, to suit particular applications by changing component materials and/or braiding variables.
These and other objects o the invention are achieved with a novel prosthesis for use in repairing or replacing soft tissue comprising a triaxially-braided fabric element containing interwoven first, second and third sets of fibers, with the fibers of said first set being oriented in substantially the same direction, the fibers of said second and third sets being oriented at substantially the same acute braiding angle with respect to the fibers of the first set, and the fibers of one of said three sets having greater elasticity than the fibers of one or both of the other two of sai.d three sets. One important embodiment of the novel prosthesis of the invention is a prosthesis adapted for use in repairin~
or replacing ligament or tendon tissue, in which embodi-ment the prosthesis has first and second opposed end portions adapted to be attached with the prosthesis in tension to the body of a patient, with said two end portions defining between them the longitudinal direction of the prosthesis, the fibers of the first set are oriented in substantially said longitudinal direction of the prosthesis, the fibers of the first set have greater elasticity than the fibers of both of said second and third sets, and the fibers of the second and third sets have greater yield strength and Young's modulus than the fibers of the first set. By increasing (or decreasing) the ~2~
braiding angle with oth~r variables fixed, the resistance of this ligament or tendon prosthesis to deformation under longitudinal loading may be decreased (or increased~.
Preferably, the fibers of the second set in the ligament or tendon prosthesis are identical with the fibers of the third set. In a preferred design for a ligament or tendon prosthesis of the invention, the fabric element of said prosthesis has the shape of a cylindrical tube, the fibers of the first set are oriented in the longitudinal direction of said tube and ~he fibers of the second and third sets are helically-disposed in the wall of said tube.
The broad conception of the present invention comprises numerous other embodiments in addition to the ligament or tendon prosthesis discussed in the preceding paragraph, such as a vascular graft prosthesis in which the woven fabric element has the shape of a cylindrical tube, the fibers of the first set are oriented in the longitudinal direction of said tubel the fibers of the second and third sets are helically-disposed in the wall of said tube, and the fibers ofthe first set have greater elasticity than the fibers of both of said second and third sets. The present invention also includes a prosthetic heart valve leaflet in the form of a sheet in which the fibers of the first set are oriented in ~he cixcumferential direction of the valve and have greater yield strength and Youngls modulus than the fibers of the second and third sets, and the fibers of the second and third sets have greater elasticity than the fibers of the first set.
6~:~
As used herein, the terms "yield strength" and "yield stress" are synonymous and refer to the tensile stress (in units of force per unit cross~sectional area) at which significant (l.e. greater than 0.2~ of initial length) plastic deformation of a naturally-occurring or synthetic object occurs. The term "Young's modulus" refers to the ratio of the tensile stress placed on an object in elastic deformation to the resulting longitudinal strain. The ~erm "elasticity"
refers to the amount of recoverable elongation of a tensioned article, i~e. the percent elongation (expressed as a percentage of initial length) at the yield stress defined above~ ~ote that as a matter of definition a "highly elastic" material (i.e. a material exhibitiny a high elasticity) may be either highly resistant to elastic deformation (high Young's modulus) or not (low Young's modulus).
The invention will be described in detail with reference to a preferred embodiment thereo, which is a ligament prosthesis. Reference to this embodiment does not limit the scope of the invention, which is limited only by the scope of the claims.
In the drawings:
FIG. 1 is a perspectiva view of a ligament pros~hesis oE the invention;
FIG. 2 is an enlarged view of the braided structure of the prosthesis of FIG. l;
FIG. 3 is a schematic representation of the load-strain behavior of the prosthesis of FIG. 1, showing the effect o braiding angle; and FIGS. 4 and 5 depict the load-strain behavior of particular ligament prostheses of the invention.
6~
A ligament prosthesis 1 of the invention, which consists of a triaxially-braided fabric element 3 havlng opposed end portions 5 and 7 defining between them the longitudinal direction of the pros~hesis, is shown in FIG. 1. In the embodimenl: shown in FIG. 1, prosthesis 1 and fabric element 3 are coincident, but (as will be explained below) this is not always necessarily so. Fabric element 3 in FIG. 1 has the form of a seamless cylindrical tube; although only a portion of the braided structure of fabric element 3 is shown in FIG. 1, it is to be understood that said braided structure actually extends along the entire length of element 3 from end portion 5 to end portion 7.
An enla~ged view of the braided structure of fabric element 3 i5 shown in FIG. 2, in which figure the vertical direction is the longitudinal direction of the prosthesis.
Fabric element 3 contains interwoven first, second and third sets 9, 11 and 13, respectively, of fibers.
The fibers of first set 9 are straight and oriented in substantially the same warp direction, i.e. the longitudinal direction of the prosthesis. The weft fibers of second and third sets 11 and 13 are helically-disposed in the wall of tubular fabric element 3 (see FTG. 1~ and are oriented at substantially the same acute braiding angle A ~see FIG. 2) with respect ko the fibers of first set 9. Each fiber of set 9 is held between the fibers of sets 11 and 13. The weft fibers of sets 11 and 13 are preferably disposed in a two-up and two-down manner with respect to one another and in a one-up and one-down manner with respect to the ~(36~
fibers of set 9. Other braiding patterns may alternatively be employed, such as the disposition of the fibers of sets 11 and 13 with respect to one another in a one-up and one-down or two up and one-down manner. In FIG. 2, braiding angle A is about 30. Preferably, all of the fibers in fabric element 3 have circular cross-sections of about the same diame~er. If desired, various fibers in one or both of the sets 11 and 13 may be dyed to provide a means to indicate the degree of tension and elongation being experienced by the prosthesis. For example, as illustrated in FIG. 1, two fibers in each helical set may be dyed. As the prosthesis is tensioned, the spacing between the dyed fibers increases according to a predetermined relationship between tensile load and strain for the prosthesis. Thus, if implantation in a pretensioned state is desirable, the surgeon may be provided with a linear gauge showing the desired dyed fiber spacing at a desired state of pretension for the prosthesis.
Triaxially-braided fabrics such as the one depicted in FIG. 2 and the methods of manufacturing them in different configurations (flat sheets, tubes, patches, strips, etc.) are well known to those skilled in the art of manufacturing braided polymeric articles (see for example U.S. Patents 4,191,218; 4,192,020 and 4,297,749).
Braiding angles of from about 10 to about 80 are attainable. A significant advantage of using a triaxially-braided fabric element such as element 3 as a ligament prosthesis is that the element can be readily implanted in a tensioned state by attaching its two end portions, _ ~ 5 and 7, to the body of a ~:2~6~
_9_ patient (for example to the two bones making up a joint or to the two free ends of a severed natural ligament) by means of simple stapling or suturing techniques. Of course, if desired, a ligament or tendon prosthesis of the invention may include, in addition to a triaxially-braided fabric element, distinct means ~for example those disclosed in U.S. Patent 4,246,660) attached to the end portions of the fabric element for securing the prosthesis to the body of the patient.
In the ligament prosthesis 1 depicted in FIGS. 1 and 2 the longitudinally-orîented straight inlaid fibers of set 9 have greater elasticity than the fibers of helically-disposed sets 11 and 13, while the fibers of sets 11 and 13 have greater yield strength and Young's modulus than the fibers of set 9. As a result, the set 9 fibers provide the ligament prosthesis with the desired elasticity, while the set 11 and set 13 ibers provide the desired strength and resistance to longitudinal tensile deformation of the composite prosthetic article.
The applied axial tensile load - % axial elongation curve for prosthesis 1 (not pretensioned) is shown schematically as curve C in FIG. 3. Initially, the slope of the load vs. elongation curve is ~uite low as the load is borne primarily by the elastic fibers of set 9. As elongation increases, however, the helically-disposed fibers of sets 11 and 13 become more aligned with the direction of elongation. As a result the slope of the load vs. elo~ga~ion curve for the prosthesis increases sharply in the vicinity o point P3. Eventually ~;~2~
--10~
the yield point of the prosthesis is reached, which is essentially equal to the yield poin~ of the woven assembly of the fibers of sets ll and 13. An important characteristic of prosthesis l is the orientation of the elastic fibers of se~ 9 in the longitudinal direction of the prosthesis, which permits the storage of a large amount of elastic energy in the elongating fibers of this set. Significant additional elastic energy is stored in the compression of the fibers of set 9 by ~he fibers of sets 11 and 13 during elongation of the prosthesis. Only a small amount of appliecl work is dissipated as friction.
The fibers of the interwoven three sets in a prosthesis of the invention are preferably made of synthetic polymeric materials, although naturally-occurring (e.g. silk) and inorganic (e.~. stair.less steel) fibers may also be used. If desired, biologically resorbable fibers may be employed. It is usually preferred that the fibers of the second and third sets be identical and equal in number.
The elastic fibers of the first set in a ligament and/or tendon prosthesis of the invention such as prosthesis l may, for example, be selected from the group consisting of polyurethane polymers, silicone elastomers, polyester/
polyether block copolymers, spandex-type polyurethane/polyethex block copolymers, spandex-type polyurethane/polyester block copolymers, and hard elastic polypropylene.
The strong and stiff fibers of the second and third sets in such a prosthesis may, for example, be selected from the group consisting of polyethylene-terephthalate, nylon, aromatic polyamide polymers ~2~
`,. ~.
such as Kevlar (E.I. du Pont de Nemours & Co~;
Wilmington, Del.), isotactic polypropylene, poly~lycolic acid and polylactic acid. Other suitable materlals are readily apparent to those skilled in the art of polymer chemistry, As just one specific example, the fibers of first set 9 of prosthesis 1 rnay be made of a polyester/polyether block copolymer such as Hytrel~(DuPont) and the fibers of sets 11 and 13 of polyethyleneterephthalate. Other alternative coznbinations of fibers are listed (non-exclusively) below:
,Y ~f~J~
~12--O ~ ~ ~ O ~ O
o ~a ~ ~ ~ o E~ ~4 u ~a h ~ U ~ ~
~1 0 U ~ a) a) ~1 o u r-l O
O ~ ~ O ~ ~1 0 ~:
O Q. ~1 Ua) a~ ~ ~1 ~ a U~ U O ~rl ~ ~1 0 O ' U rl U ~ ~ ~ V '1-l U U
U .5:: S ~ rl S
U ~ ) U r l ~ ~
o ~ o e ~ ~ o o ~ :~ o -1 0 0 r t r-l r~l r t r-t O O r~ ~--I r~ O rl r-t 0 0 0 0 0 ~ ~ O ~~1 ~ O
~0 ~rl p~ rt Q~ P~
h $~1 h $ ~ ~
r t t~ r-l rt -t ~ rt rt r t o a~ (I) 1~ 0 a~ 1~1 0 P~ r~ S S p~ r l S Q~
r~) o ~J P~ ~ ~ O ~ P.~ ~a rl ~ rl ~ ~r l a) ~rl aJ
e ~ u ~ ~ h 1~3 P~ U
rl --t ~ ~t U ~) ~ ~ r-l ~ ~ ~IJ
r-t O U ~a ~ a) r t O O C) rt O ~ ~rl ~ ~ O ~ ~ 0 O p~ r-t U tU ~ P~ rt G~ ~ a) U~ O O ~rl r l rt U O ~I r-t C) ~rt U ~ ~ ~ U ~rl U ~1 U
~rl ~ ~ U ,5~ -1 IJ ~ ,C ~rl ,~
U r t t~
o ~ o ~ o e ~ o r~t O O r~ r-l rl r-l r~ O O r~ r~ r~ O rt r t O O O O ~t S-l ~1 0 0 ~1 ~1 0 ~1 p p~ rt a) ~ G~
h ~ O O O ~Q' a) ~ n~ u t U ~`
a)O ~ h S )~ t r t rt r~ r~l rt ~tE~ ) O ~ aJ ~ al r~ C) r~ U
o o o o o o o o o o o ~ ~ a) e a) e O O O O
Q~ ~ ~ ~ PJ P~ l ~ r-l \~
tJ'~ ttl' 11~ fJ 0 r~ ~t r--i r~t r~ r~ J St o ~) a) OJ a) a) tr~ ~) (a td ~tt O O O O O O ~
r~ ~tr~ l r t Ql P~ ~ ~ P~ t ~\
a) ~ ~ o ~ o ~ o U~ ~ ~ ~ ~ ~ ~ ~ U ~ U ~ U ~ ~ ~ .C
h h 5~ i O O O O O v~ U u~ V 0 t) ~ ~ a) ~
U U t) t) U Ql O a) O a) O ~a r t r~ r-t ~C
~ ~ ~ ~ rl rtrt rl r~t ~ r l ~ r-l ~ r~ ~ O ~ O
rt r~ ~t r~l r~l r-l rt ~t r~i rt rt r~t ,q r~ 5~ ~J ,4 /~ p~ 0 P~
O O OO O O ~rl ~rl ~rl ~rl rl O O O . ~I P~
P~ P~ P~ ~ ~ 0 0 0 tll 0 ~ P~ P~ bq 0 ,' ~
:~L2;~6C3~' a) ~ a~ a O O
E~ h O ~1 a O ~1 0 O ~ r-l ~ a) a U~ O ~i r-~
~ O
O ~1 ~1 0 ~1 ~1 h O :~ h O O
i>1 ~ ~
~1 ~ ~ ,1 0~ ~ .C ~
U ~ h 5-1 ~I ~ U >1 ~ O ~ 0 U~ O ~ _l U ~ U
o ~ ~l o ~ ~l $
h 0~ ~ ~ ~C p~
a~ o ~ o ~ o a~ o a) o o O --I O ~I t~ _I U _I U
O O O O O O O O .0 0 0 U~ ~ ~S ~ ~ ~ U~
x a) x ~J x 1) X o x ~ o ~ o ~ o ~ o ~ o ~
Aside from the materials selected for the three sets of fibers in a prosthesis of the invention and the overall configuration and dlmensions of the prosthesis, the resulting mechanical properties of the prosthesis, e g. prosthesis 1 in FIGS. 1 and 2, are also materially affected by the various braidîng variables, e.g. the fiber diameters, braiding angle, braiding tension, density of windings, number ratio of fibers in the three sets and braiding pattern. Of considerable impor~ance is the braiding angle, illustrated as angle A in FIG. 2. As is shown schematically in FIG. 3, the resistance of prosthesis 1 to deformation under axial loading in tension increases as the braiding angle is decreased (curve A to curve D).
Fuxthermore, the percent elongation of prosthesis 1 (as a percentage of initial length) at whi.ch significant plastic deformation or breakage of the prosthesis co~ences decreases as the braiding angle is decreased.
Thus it can be seen that, with all other variables fixed, the load-strain behavior of prosthesis 1 can be adjusted to approximate that of a natural ligament or tendon sought to be repaired or replaced by varying the braiding angle. Additionally, with all other variables fixed and the fibers of the sécond and third sets identical and equal in number, the load-strain behavior of prosthesis 1 can be substantially adjusted by varying the numerical ratio of fibers in the three sets, e.~. from 1 (longitudinal): 1 (helical): 1 (helical) to 0.5 (longitudinal): 1 (helical): 1 (helical), while main-taining a balanced prosthesis. The above-indicated change in number ratio would render the prosthesis more resistant to elongation under axial lvading i~ tension.
In addition to mechanical properties, the wall porosity of ~ prosthesis of the invention may be varied in a predictable manner by altering the braiding variables, particularly the fiber diameters, braiding tension and density of windings. A relatively high porosity permits, if desired, substan~ial tissue ingrowth into the wall of the fabric element of the prosthesis, while a relatively low porosity minimizes such ingrowth if it is not desired. Generally, tissue ingrowth is desired in a permanent prosthesis but not in a temporary one.
The triaxially-braided fabric element of a ligament and/or ~endon pros~hesis of ~he invention may have other shapes than the cylindrical tube shown in FIG. 1. Thus, the fabric element may have the shape of a flattened cylindrical tube. As another example, the fabric element of a ligament and/or tendon prosthe~is may have the shape of a flat elongated strip, in which the straight, longitudinally-oriented elastic fibers of the first set are disposed in essentially a single plane and each of the fibers of the second and third sets traverses said plane in a zig-zag manner (as depicted in FlG. 9 of U.S. Patent 4,191,218) while malntaining a constant braiding angle.
The present invention is by no means limited to ligament and/or tendon prostheses, but includes prostheses for other soft tissue structures as well (e ~., blood vessels). Thus, for example, a vascular prosthesis of the inven~ion such as an aortic graft prosthesis may have the same shape (but typically a ~z~
different diameter) as the prosthesis 1 shown in FIG.
1. In such a vascular prosthesis, the fibers of sets 9, 11 and 13 are all elas~ic, with the straight fibers of longitudinally-oriented set 9 being more or less elastic, preferably more elastic, than the fibers of both of the other two sets. Accordingly, a tubular vascular prosthesis may be provided with high elasticity in the longitudinal directi~n as well as substantial elasticity in the radial direction to accomodate the pulsing flow of blood ln vivo. If desired, such a tubular vascular prosthesis may include an impermeable elastic internal coating or tubular insert.
Additionally, a heart valve prosthesis of the invention may comprise a frame having a generally circular base defining the circumferential direction of the prosthesis and a plurality of spaced, generally parallel legs extending from the base; and a plurality of triaxially-braided fabric elements having the form of sheets and attached by conventional means to the frame in such a manner that they function as heart valve leaflets during the operation of the valve.
Preferably, in each of said fabric elements, the fibers of ~he first set are oriented in ~he circumferential direction of the valve when the valve is in the open position, the fibers of the second and third sets traverse the first set of fibers in a zig-zag manner (as depicted in FIG. g of U.S. Paten~ 4,191,218), the fibers of the first set have greater yield strength and Young's modulus than the fibers of the second and third sets, and the fibers of the second and third se-t~
have grea-ter elasticity than the ~ibers of the ~irs~
set. Accordingly, an arti~icia] heart valve prosthesis leaflet is provided that is capable of substalltial elas-tic stretching in directions generally or-thogonal to the circular base of the frame of the heart valve prosthesis.
The use of prostheses of the invention to repair or replace soft tissue re~uires only simple surgical procedures. Af-ter diseased or damaged soft tissue has been removed, the ends o~ a prosthesis of the invention may be readily at-tached to bone (e.g. with conventional bone staples) or to soft -tissue (e.g.
by su~uring). Prostheses of the present invention may be cut to a desired length without unravelling~
If desired, two tubular prostheses of the invention may be readily anastomosed in an end-to-end fashion.
To r?revent fraying of the triaxially-braided Eabric element the free ends of the fibers at the edge of the element may be fu~ed together, e.g. hy ul-trasorllc welding or by dipping the edge of the element in a suitable coating material~ A ligament and/or tendon prosthesis of the invention may be precondi-tiorled before use by applying and releasing an a,~ial tensile load ~e.g. 60 lbs ) a number of times. In the case of an anterior cruciate ligament prosthesis, the prosthesis is preferably implanted in a lonyitudinally pretensioned s-tate. Then, the obs-erved load-strain behavio~ of -the implanted prosthesis is that relative to an origin such as the origin O' on curve C defined by the dotted abscissa and ordinate in FIG. 3.
~22~6~
Conventional techniques (see for example the article by James, S. L., "Biomechanics of Knee Ligament Reconstruction", Clin. Orthoped. and Related Res., No. 146, pp. 90-101 (Jan.-Feb. 1980)~ may be employed in attaching a ligament prosthesis oE the invention to the patient's body. Preferably, ~ short end length of the prosthesis (e.g. prosthesis l) is folded over once (i.e. lap folded) and the attachment to the body effected at this doubled region. The suxgical joining of a severed natural tendon may be facilitated by slipping a tubular prosthesis of the invention over the free end of one portion of the severed tendonr surgically joining the two portions of the tendon and then attaching the prosthesis to ~he two respective portions of the severed tendon. The prosthesis serves to suppor~ the healing tendon and can be removed after the healing has been accomplished.
By appropriate selection of braiding and other variables the mechanical properties of various natural human ligaments and tendons can be closely approximated by a prosthesis of the present invention. Often, in order to make such a match, it is desixed that the prosthesis exhibit a tensile break point of at least about 75 kg. and, after initial pretension, an overall load modulus of from about 200 kg./(unit of strain based on pretensioned length) to about 600 kg./(unit of strain based on pretensioned length) over a range of substantially recoverable tensile elongation beginning at the pretensioned state and extending over a strain equal to at least about 25 percent of the initial pretensioned length of the 6~1 prosthesis. Two examples of prosthesis 1 having these desired properties are set forth below. These examples are not to be construed as limiting the invention.
EXAMPLE 5 Set 9 - Longitudinal fibers - 48 ends - Hytrel Type 5556 polyester/polyether block copolymer monofilament ~E.I. du Pont de Nemours & Co.;
Wilmington, Del.) - 220 denier Set 11 - Helical fibers - 46 ends of 220 denier ~ acron Type 52 polyethyleneterephth~late twisted multifilament (Du Pont) and 2 ends of 250 denier Dacron~Type 55 polyethylene-terephthalate twisted multifilament (Du Pont) dyed with D & C green dye No. 6 Set 13 - Helical fibers - same as set 11 Prosthesis configuration - flattened circular cylindrical tube 1.5 inches in length - 21 mm. circumference Braiding angle 45 Braiding pattern of sets 11 and 13 with respect to one another - 2-up and 2-down Density of windings of sets 11 and 13 -35 picks per inch Braiding tension - 50 to 55 g. on longitudinal fibers, 3 oz. braider carrier springs on helical fibers The above-described prosthesis exhibited the load-strain behavior shown in FIG. 4 (the origin is drawn with reference to the untensioned state). The pros~hesis exhibits a tensile break point of 250 lbs. = 113 kg.
If the prosthesis is pretensioned to, for example, 10 l~s. tension (20% strain), it will exhibit an ~ e ~,o,~
~2;~6~
overall load modulus over a range of 37~ of the pretensioned length cf the prosthesis (equivalent to 44% of untensioned length~ of (250-10) lbs./(.37 unit of strain) = 295 kg./
(unit of strain). Above 20 lbs. load, the prosthesis will exhibit a substantially constant load modulus of (250-20) lbs./(0.31 unit of strain) = 340 kg./(unit of strain). No distinct yield point is observed prior to breakage.
EXAMPLE 2 0 Set 9 - Longitudinal fibers - 48 ends - Lycra Type 127 spandex-type polyurethane/polyether block copolymer coalesced multifilament (du Pont) - 280 denier Sets 11 and 13 - Helical fibers - same as in Example 1 5 Prosthesis configuration - same as in Example 1 except that circumference of tube is 19 mm.
Braiding angle - 48 Braiding ~)attern of sets 11 and 13 with respect to one another - 2-up and 2-down Densi.ty of -~indings of sets 11 and 13 -42 picks per inch Braiding tension - 20 to 25 g. on longitudinal fibers, 3 oz. braider carrier springs on helical fibers The above-described prosthesis exhibited the load-strain behavior shown in FIG. 5 (the origin is drawn with reference to the untensioned state). The prosthesis exhibits a tensile break point of 202 lbs. = 92 kg.
If the prosthesis is pretensioned to, for example, 7 Ibs. tension (40% strain), it will exhibit an overall load modulus over a range of 29~ of the pretensioned length of the prosthesis (equivalent to 40g of untensioned length) of (202-7) lbs./(.29 unit of strain) = 305 kg./
tunit of strain). Above 20 lbs. load, the prosthesis will exhibit a substantially constant load modulus of (202-20) lbs./(0.23 unit of strain) = 360 kg./(unit of strain). No dis~inct yield point is ob~erved prior to breakage.
TRIAXIhEEY~RhIDED FABRIC ~OSTHESIS
The na~ural ligaments are elongated bundles of collag-enous soft tissue that serve, amo~g other things, to hold the component bones of joints toge~her. The surgical treatment of diseased or damaged ligaments, e.g.
the anterior cruciate ligamen~, has been severely hampered bv the una~ailability of a suitable, generally accepted ligament prosthesis. The desired character-istics for a li~ament prosthesis include appropriate size and shape, biological compatibility, capability of being readily attached by the surgeon to the body of the patient, high fatigue resistance and mechanical behavior approximating that of the ligamentous tissue sought to be repaired or replaced.
The latter desired characteristic is particularly important. Natural ligaments are both strong and highly elastic, which qualities are generally not found together in a single material. Thus, for example, the anterior cruciate ligament of normal adult humans exhibits a yield point in ten~ion of about 50 kg. at a reversible elongation of about 28%, and a break point of about 60 kg~ (Typical adult human tendons are stronger and less elastic.) A number of ligam~nt and/or tendon pr~stheses are known in which the load bearing body portion is fabricated essentially of a single ~ynthetic material (see, e~ , U.S. Patents 3,176,316; 3,613,120;
4,127,g02; 4,149,277; 4,20g,859; 4,255,820; 4,329,743 and 4,345,339; U.K. ~atent 1,602,834 and European Published Patent Appln. 51,954). These monocomponent devices generally possess insufficient longitudinal elasticity and some also exhibit inadequate lcngitu-dinal break strength. As a result of their insufficient elasticity, this type of prosthesis must be forced into the region of plastic deformation to achieve the lonyitudinal elongation desired for normal anatomical function, e.g. flexion of a joint, which o course permanently impairs the mechanical function of the prosthesis.
~ ecently, ligament prostheses have been disclosed in U.S. Paten~s 4,246,660 and 4,301,551 in which the load bearing body portion is a bicomponent structure comprised of one material that imparts strength to the prosthesis and another ma~erial that imparts elasticity. The use of these prostheses alleviates the disadvantages described above for the monocomponent type of prosthesis.
However, the prostheses disclosed in the '660 and '551 Patents are complex in construction and their methods of attachment to the body of the patient involve rather complicated surgical procedures.
A recent thesis (Elizabe~h E. Fitzgerald, "Mechanical E,ehavior of Bicomponent Braids as Potential Surgical Implants", Master of Science Thesis, Cornell University, August 1979) has disclosed the use of a braided bicom-ponent tube as a ligament prosthesis. In this pros-thesis two interwoven sets of polymeric fibers, one of a strong material and the other of an elastic material, are helically-disposed in the wall of the tube and oriented at a fixed angle with respect to one another.
~6g~' Each set of fibers is oriented at the same acuke angle with respect to the longitudinal direction of the tube.
The prosthesis may additionally comprise a monocomponent polymeric filament core.
The prosthesis disclosed in the Fitzgerald thesis has certain inherent disadvantages. First, since the fibers in the two helically-disposed interwoven sets are not idential, the prosthesis is not balanced and will tend to twist during longitudinal elongation.
Second, since the set of helically-disposed elastic fibers is angulated with respect to the longitudinal direction of the prosthesis, only a minor amount of the work performed in elongating the prosthesis longi-tudinally is converted to elastic energy stored in the extended set of elastic fibers. Undesirably large portions of said work are converted to elastic energy stored in the other set of strong fibers or dissipated as ~riction in the extending trellis-like bicomponent braided structure.
It is an object of the present invention to provide a ligament prosthesis of simple construction that exhibits a yield strength in tension and a longitudinal elasticity that are a~ least comparable to that of a human ligament and a resistance to longitudinal elastic deformation in tension that approximates that of a human ligament.
Is ls another object of the invention to provide a balanced braided prosthesis of such construction that its longitudinal load-strain behavior can be readily "fine-t~ned", while maintaining balance, to suit particular applications by changing component materials and/or braiding variables.
These and other objects o the invention are achieved with a novel prosthesis for use in repairing or replacing soft tissue comprising a triaxially-braided fabric element containing interwoven first, second and third sets of fibers, with the fibers of said first set being oriented in substantially the same direction, the fibers of said second and third sets being oriented at substantially the same acute braiding angle with respect to the fibers of the first set, and the fibers of one of said three sets having greater elasticity than the fibers of one or both of the other two of sai.d three sets. One important embodiment of the novel prosthesis of the invention is a prosthesis adapted for use in repairin~
or replacing ligament or tendon tissue, in which embodi-ment the prosthesis has first and second opposed end portions adapted to be attached with the prosthesis in tension to the body of a patient, with said two end portions defining between them the longitudinal direction of the prosthesis, the fibers of the first set are oriented in substantially said longitudinal direction of the prosthesis, the fibers of the first set have greater elasticity than the fibers of both of said second and third sets, and the fibers of the second and third sets have greater yield strength and Young's modulus than the fibers of the first set. By increasing (or decreasing) the ~2~
braiding angle with oth~r variables fixed, the resistance of this ligament or tendon prosthesis to deformation under longitudinal loading may be decreased (or increased~.
Preferably, the fibers of the second set in the ligament or tendon prosthesis are identical with the fibers of the third set. In a preferred design for a ligament or tendon prosthesis of the invention, the fabric element of said prosthesis has the shape of a cylindrical tube, the fibers of the first set are oriented in the longitudinal direction of said tube and ~he fibers of the second and third sets are helically-disposed in the wall of said tube.
The broad conception of the present invention comprises numerous other embodiments in addition to the ligament or tendon prosthesis discussed in the preceding paragraph, such as a vascular graft prosthesis in which the woven fabric element has the shape of a cylindrical tube, the fibers of the first set are oriented in the longitudinal direction of said tubel the fibers of the second and third sets are helically-disposed in the wall of said tube, and the fibers ofthe first set have greater elasticity than the fibers of both of said second and third sets. The present invention also includes a prosthetic heart valve leaflet in the form of a sheet in which the fibers of the first set are oriented in ~he cixcumferential direction of the valve and have greater yield strength and Youngls modulus than the fibers of the second and third sets, and the fibers of the second and third sets have greater elasticity than the fibers of the first set.
6~:~
As used herein, the terms "yield strength" and "yield stress" are synonymous and refer to the tensile stress (in units of force per unit cross~sectional area) at which significant (l.e. greater than 0.2~ of initial length) plastic deformation of a naturally-occurring or synthetic object occurs. The term "Young's modulus" refers to the ratio of the tensile stress placed on an object in elastic deformation to the resulting longitudinal strain. The ~erm "elasticity"
refers to the amount of recoverable elongation of a tensioned article, i~e. the percent elongation (expressed as a percentage of initial length) at the yield stress defined above~ ~ote that as a matter of definition a "highly elastic" material (i.e. a material exhibitiny a high elasticity) may be either highly resistant to elastic deformation (high Young's modulus) or not (low Young's modulus).
The invention will be described in detail with reference to a preferred embodiment thereo, which is a ligament prosthesis. Reference to this embodiment does not limit the scope of the invention, which is limited only by the scope of the claims.
In the drawings:
FIG. 1 is a perspectiva view of a ligament pros~hesis oE the invention;
FIG. 2 is an enlarged view of the braided structure of the prosthesis of FIG. l;
FIG. 3 is a schematic representation of the load-strain behavior of the prosthesis of FIG. 1, showing the effect o braiding angle; and FIGS. 4 and 5 depict the load-strain behavior of particular ligament prostheses of the invention.
6~
A ligament prosthesis 1 of the invention, which consists of a triaxially-braided fabric element 3 havlng opposed end portions 5 and 7 defining between them the longitudinal direction of the pros~hesis, is shown in FIG. 1. In the embodimenl: shown in FIG. 1, prosthesis 1 and fabric element 3 are coincident, but (as will be explained below) this is not always necessarily so. Fabric element 3 in FIG. 1 has the form of a seamless cylindrical tube; although only a portion of the braided structure of fabric element 3 is shown in FIG. 1, it is to be understood that said braided structure actually extends along the entire length of element 3 from end portion 5 to end portion 7.
An enla~ged view of the braided structure of fabric element 3 i5 shown in FIG. 2, in which figure the vertical direction is the longitudinal direction of the prosthesis.
Fabric element 3 contains interwoven first, second and third sets 9, 11 and 13, respectively, of fibers.
The fibers of first set 9 are straight and oriented in substantially the same warp direction, i.e. the longitudinal direction of the prosthesis. The weft fibers of second and third sets 11 and 13 are helically-disposed in the wall of tubular fabric element 3 (see FTG. 1~ and are oriented at substantially the same acute braiding angle A ~see FIG. 2) with respect ko the fibers of first set 9. Each fiber of set 9 is held between the fibers of sets 11 and 13. The weft fibers of sets 11 and 13 are preferably disposed in a two-up and two-down manner with respect to one another and in a one-up and one-down manner with respect to the ~(36~
fibers of set 9. Other braiding patterns may alternatively be employed, such as the disposition of the fibers of sets 11 and 13 with respect to one another in a one-up and one-down or two up and one-down manner. In FIG. 2, braiding angle A is about 30. Preferably, all of the fibers in fabric element 3 have circular cross-sections of about the same diame~er. If desired, various fibers in one or both of the sets 11 and 13 may be dyed to provide a means to indicate the degree of tension and elongation being experienced by the prosthesis. For example, as illustrated in FIG. 1, two fibers in each helical set may be dyed. As the prosthesis is tensioned, the spacing between the dyed fibers increases according to a predetermined relationship between tensile load and strain for the prosthesis. Thus, if implantation in a pretensioned state is desirable, the surgeon may be provided with a linear gauge showing the desired dyed fiber spacing at a desired state of pretension for the prosthesis.
Triaxially-braided fabrics such as the one depicted in FIG. 2 and the methods of manufacturing them in different configurations (flat sheets, tubes, patches, strips, etc.) are well known to those skilled in the art of manufacturing braided polymeric articles (see for example U.S. Patents 4,191,218; 4,192,020 and 4,297,749).
Braiding angles of from about 10 to about 80 are attainable. A significant advantage of using a triaxially-braided fabric element such as element 3 as a ligament prosthesis is that the element can be readily implanted in a tensioned state by attaching its two end portions, _ ~ 5 and 7, to the body of a ~:2~6~
_9_ patient (for example to the two bones making up a joint or to the two free ends of a severed natural ligament) by means of simple stapling or suturing techniques. Of course, if desired, a ligament or tendon prosthesis of the invention may include, in addition to a triaxially-braided fabric element, distinct means ~for example those disclosed in U.S. Patent 4,246,660) attached to the end portions of the fabric element for securing the prosthesis to the body of the patient.
In the ligament prosthesis 1 depicted in FIGS. 1 and 2 the longitudinally-orîented straight inlaid fibers of set 9 have greater elasticity than the fibers of helically-disposed sets 11 and 13, while the fibers of sets 11 and 13 have greater yield strength and Young's modulus than the fibers of set 9. As a result, the set 9 fibers provide the ligament prosthesis with the desired elasticity, while the set 11 and set 13 ibers provide the desired strength and resistance to longitudinal tensile deformation of the composite prosthetic article.
The applied axial tensile load - % axial elongation curve for prosthesis 1 (not pretensioned) is shown schematically as curve C in FIG. 3. Initially, the slope of the load vs. elongation curve is ~uite low as the load is borne primarily by the elastic fibers of set 9. As elongation increases, however, the helically-disposed fibers of sets 11 and 13 become more aligned with the direction of elongation. As a result the slope of the load vs. elo~ga~ion curve for the prosthesis increases sharply in the vicinity o point P3. Eventually ~;~2~
--10~
the yield point of the prosthesis is reached, which is essentially equal to the yield poin~ of the woven assembly of the fibers of sets ll and 13. An important characteristic of prosthesis l is the orientation of the elastic fibers of se~ 9 in the longitudinal direction of the prosthesis, which permits the storage of a large amount of elastic energy in the elongating fibers of this set. Significant additional elastic energy is stored in the compression of the fibers of set 9 by ~he fibers of sets 11 and 13 during elongation of the prosthesis. Only a small amount of appliecl work is dissipated as friction.
The fibers of the interwoven three sets in a prosthesis of the invention are preferably made of synthetic polymeric materials, although naturally-occurring (e.g. silk) and inorganic (e.~. stair.less steel) fibers may also be used. If desired, biologically resorbable fibers may be employed. It is usually preferred that the fibers of the second and third sets be identical and equal in number.
The elastic fibers of the first set in a ligament and/or tendon prosthesis of the invention such as prosthesis l may, for example, be selected from the group consisting of polyurethane polymers, silicone elastomers, polyester/
polyether block copolymers, spandex-type polyurethane/polyethex block copolymers, spandex-type polyurethane/polyester block copolymers, and hard elastic polypropylene.
The strong and stiff fibers of the second and third sets in such a prosthesis may, for example, be selected from the group consisting of polyethylene-terephthalate, nylon, aromatic polyamide polymers ~2~
`,. ~.
such as Kevlar (E.I. du Pont de Nemours & Co~;
Wilmington, Del.), isotactic polypropylene, poly~lycolic acid and polylactic acid. Other suitable materlals are readily apparent to those skilled in the art of polymer chemistry, As just one specific example, the fibers of first set 9 of prosthesis 1 rnay be made of a polyester/polyether block copolymer such as Hytrel~(DuPont) and the fibers of sets 11 and 13 of polyethyleneterephthalate. Other alternative coznbinations of fibers are listed (non-exclusively) below:
,Y ~f~J~
~12--O ~ ~ ~ O ~ O
o ~a ~ ~ ~ o E~ ~4 u ~a h ~ U ~ ~
~1 0 U ~ a) a) ~1 o u r-l O
O ~ ~ O ~ ~1 0 ~:
O Q. ~1 Ua) a~ ~ ~1 ~ a U~ U O ~rl ~ ~1 0 O ' U rl U ~ ~ ~ V '1-l U U
U .5:: S ~ rl S
U ~ ) U r l ~ ~
o ~ o e ~ ~ o o ~ :~ o -1 0 0 r t r-l r~l r t r-t O O r~ ~--I r~ O rl r-t 0 0 0 0 0 ~ ~ O ~~1 ~ O
~0 ~rl p~ rt Q~ P~
h $~1 h $ ~ ~
r t t~ r-l rt -t ~ rt rt r t o a~ (I) 1~ 0 a~ 1~1 0 P~ r~ S S p~ r l S Q~
r~) o ~J P~ ~ ~ O ~ P.~ ~a rl ~ rl ~ ~r l a) ~rl aJ
e ~ u ~ ~ h 1~3 P~ U
rl --t ~ ~t U ~) ~ ~ r-l ~ ~ ~IJ
r-t O U ~a ~ a) r t O O C) rt O ~ ~rl ~ ~ O ~ ~ 0 O p~ r-t U tU ~ P~ rt G~ ~ a) U~ O O ~rl r l rt U O ~I r-t C) ~rt U ~ ~ ~ U ~rl U ~1 U
~rl ~ ~ U ,5~ -1 IJ ~ ,C ~rl ,~
U r t t~
o ~ o ~ o e ~ o r~t O O r~ r-l rl r-l r~ O O r~ r~ r~ O rt r t O O O O ~t S-l ~1 0 0 ~1 ~1 0 ~1 p p~ rt a) ~ G~
h ~ O O O ~Q' a) ~ n~ u t U ~`
a)O ~ h S )~ t r t rt r~ r~l rt ~tE~ ) O ~ aJ ~ al r~ C) r~ U
o o o o o o o o o o o ~ ~ a) e a) e O O O O
Q~ ~ ~ ~ PJ P~ l ~ r-l \~
tJ'~ ttl' 11~ fJ 0 r~ ~t r--i r~t r~ r~ J St o ~) a) OJ a) a) tr~ ~) (a td ~tt O O O O O O ~
r~ ~tr~ l r t Ql P~ ~ ~ P~ t ~\
a) ~ ~ o ~ o ~ o U~ ~ ~ ~ ~ ~ ~ ~ U ~ U ~ U ~ ~ ~ .C
h h 5~ i O O O O O v~ U u~ V 0 t) ~ ~ a) ~
U U t) t) U Ql O a) O a) O ~a r t r~ r-t ~C
~ ~ ~ ~ rl rtrt rl r~t ~ r l ~ r-l ~ r~ ~ O ~ O
rt r~ ~t r~l r~l r-l rt ~t r~i rt rt r~t ,q r~ 5~ ~J ,4 /~ p~ 0 P~
O O OO O O ~rl ~rl ~rl ~rl rl O O O . ~I P~
P~ P~ P~ ~ ~ 0 0 0 tll 0 ~ P~ P~ bq 0 ,' ~
:~L2;~6C3~' a) ~ a~ a O O
E~ h O ~1 a O ~1 0 O ~ r-l ~ a) a U~ O ~i r-~
~ O
O ~1 ~1 0 ~1 ~1 h O :~ h O O
i>1 ~ ~
~1 ~ ~ ,1 0~ ~ .C ~
U ~ h 5-1 ~I ~ U >1 ~ O ~ 0 U~ O ~ _l U ~ U
o ~ ~l o ~ ~l $
h 0~ ~ ~ ~C p~
a~ o ~ o ~ o a~ o a) o o O --I O ~I t~ _I U _I U
O O O O O O O O .0 0 0 U~ ~ ~S ~ ~ ~ U~
x a) x ~J x 1) X o x ~ o ~ o ~ o ~ o ~ o ~
Aside from the materials selected for the three sets of fibers in a prosthesis of the invention and the overall configuration and dlmensions of the prosthesis, the resulting mechanical properties of the prosthesis, e g. prosthesis 1 in FIGS. 1 and 2, are also materially affected by the various braidîng variables, e.g. the fiber diameters, braiding angle, braiding tension, density of windings, number ratio of fibers in the three sets and braiding pattern. Of considerable impor~ance is the braiding angle, illustrated as angle A in FIG. 2. As is shown schematically in FIG. 3, the resistance of prosthesis 1 to deformation under axial loading in tension increases as the braiding angle is decreased (curve A to curve D).
Fuxthermore, the percent elongation of prosthesis 1 (as a percentage of initial length) at whi.ch significant plastic deformation or breakage of the prosthesis co~ences decreases as the braiding angle is decreased.
Thus it can be seen that, with all other variables fixed, the load-strain behavior of prosthesis 1 can be adjusted to approximate that of a natural ligament or tendon sought to be repaired or replaced by varying the braiding angle. Additionally, with all other variables fixed and the fibers of the sécond and third sets identical and equal in number, the load-strain behavior of prosthesis 1 can be substantially adjusted by varying the numerical ratio of fibers in the three sets, e.~. from 1 (longitudinal): 1 (helical): 1 (helical) to 0.5 (longitudinal): 1 (helical): 1 (helical), while main-taining a balanced prosthesis. The above-indicated change in number ratio would render the prosthesis more resistant to elongation under axial lvading i~ tension.
In addition to mechanical properties, the wall porosity of ~ prosthesis of the invention may be varied in a predictable manner by altering the braiding variables, particularly the fiber diameters, braiding tension and density of windings. A relatively high porosity permits, if desired, substan~ial tissue ingrowth into the wall of the fabric element of the prosthesis, while a relatively low porosity minimizes such ingrowth if it is not desired. Generally, tissue ingrowth is desired in a permanent prosthesis but not in a temporary one.
The triaxially-braided fabric element of a ligament and/or ~endon pros~hesis of ~he invention may have other shapes than the cylindrical tube shown in FIG. 1. Thus, the fabric element may have the shape of a flattened cylindrical tube. As another example, the fabric element of a ligament and/or tendon prosthe~is may have the shape of a flat elongated strip, in which the straight, longitudinally-oriented elastic fibers of the first set are disposed in essentially a single plane and each of the fibers of the second and third sets traverses said plane in a zig-zag manner (as depicted in FlG. 9 of U.S. Patent 4,191,218) while malntaining a constant braiding angle.
The present invention is by no means limited to ligament and/or tendon prostheses, but includes prostheses for other soft tissue structures as well (e ~., blood vessels). Thus, for example, a vascular prosthesis of the inven~ion such as an aortic graft prosthesis may have the same shape (but typically a ~z~
different diameter) as the prosthesis 1 shown in FIG.
1. In such a vascular prosthesis, the fibers of sets 9, 11 and 13 are all elas~ic, with the straight fibers of longitudinally-oriented set 9 being more or less elastic, preferably more elastic, than the fibers of both of the other two sets. Accordingly, a tubular vascular prosthesis may be provided with high elasticity in the longitudinal directi~n as well as substantial elasticity in the radial direction to accomodate the pulsing flow of blood ln vivo. If desired, such a tubular vascular prosthesis may include an impermeable elastic internal coating or tubular insert.
Additionally, a heart valve prosthesis of the invention may comprise a frame having a generally circular base defining the circumferential direction of the prosthesis and a plurality of spaced, generally parallel legs extending from the base; and a plurality of triaxially-braided fabric elements having the form of sheets and attached by conventional means to the frame in such a manner that they function as heart valve leaflets during the operation of the valve.
Preferably, in each of said fabric elements, the fibers of ~he first set are oriented in ~he circumferential direction of the valve when the valve is in the open position, the fibers of the second and third sets traverse the first set of fibers in a zig-zag manner (as depicted in FIG. g of U.S. Paten~ 4,191,218), the fibers of the first set have greater yield strength and Young's modulus than the fibers of the second and third sets, and the fibers of the second and third se-t~
have grea-ter elasticity than the ~ibers of the ~irs~
set. Accordingly, an arti~icia] heart valve prosthesis leaflet is provided that is capable of substalltial elas-tic stretching in directions generally or-thogonal to the circular base of the frame of the heart valve prosthesis.
The use of prostheses of the invention to repair or replace soft tissue re~uires only simple surgical procedures. Af-ter diseased or damaged soft tissue has been removed, the ends o~ a prosthesis of the invention may be readily at-tached to bone (e.g. with conventional bone staples) or to soft -tissue (e.g.
by su~uring). Prostheses of the present invention may be cut to a desired length without unravelling~
If desired, two tubular prostheses of the invention may be readily anastomosed in an end-to-end fashion.
To r?revent fraying of the triaxially-braided Eabric element the free ends of the fibers at the edge of the element may be fu~ed together, e.g. hy ul-trasorllc welding or by dipping the edge of the element in a suitable coating material~ A ligament and/or tendon prosthesis of the invention may be precondi-tiorled before use by applying and releasing an a,~ial tensile load ~e.g. 60 lbs ) a number of times. In the case of an anterior cruciate ligament prosthesis, the prosthesis is preferably implanted in a lonyitudinally pretensioned s-tate. Then, the obs-erved load-strain behavio~ of -the implanted prosthesis is that relative to an origin such as the origin O' on curve C defined by the dotted abscissa and ordinate in FIG. 3.
~22~6~
Conventional techniques (see for example the article by James, S. L., "Biomechanics of Knee Ligament Reconstruction", Clin. Orthoped. and Related Res., No. 146, pp. 90-101 (Jan.-Feb. 1980)~ may be employed in attaching a ligament prosthesis oE the invention to the patient's body. Preferably, ~ short end length of the prosthesis (e.g. prosthesis l) is folded over once (i.e. lap folded) and the attachment to the body effected at this doubled region. The suxgical joining of a severed natural tendon may be facilitated by slipping a tubular prosthesis of the invention over the free end of one portion of the severed tendonr surgically joining the two portions of the tendon and then attaching the prosthesis to ~he two respective portions of the severed tendon. The prosthesis serves to suppor~ the healing tendon and can be removed after the healing has been accomplished.
By appropriate selection of braiding and other variables the mechanical properties of various natural human ligaments and tendons can be closely approximated by a prosthesis of the present invention. Often, in order to make such a match, it is desixed that the prosthesis exhibit a tensile break point of at least about 75 kg. and, after initial pretension, an overall load modulus of from about 200 kg./(unit of strain based on pretensioned length) to about 600 kg./(unit of strain based on pretensioned length) over a range of substantially recoverable tensile elongation beginning at the pretensioned state and extending over a strain equal to at least about 25 percent of the initial pretensioned length of the 6~1 prosthesis. Two examples of prosthesis 1 having these desired properties are set forth below. These examples are not to be construed as limiting the invention.
EXAMPLE 5 Set 9 - Longitudinal fibers - 48 ends - Hytrel Type 5556 polyester/polyether block copolymer monofilament ~E.I. du Pont de Nemours & Co.;
Wilmington, Del.) - 220 denier Set 11 - Helical fibers - 46 ends of 220 denier ~ acron Type 52 polyethyleneterephth~late twisted multifilament (Du Pont) and 2 ends of 250 denier Dacron~Type 55 polyethylene-terephthalate twisted multifilament (Du Pont) dyed with D & C green dye No. 6 Set 13 - Helical fibers - same as set 11 Prosthesis configuration - flattened circular cylindrical tube 1.5 inches in length - 21 mm. circumference Braiding angle 45 Braiding pattern of sets 11 and 13 with respect to one another - 2-up and 2-down Density of windings of sets 11 and 13 -35 picks per inch Braiding tension - 50 to 55 g. on longitudinal fibers, 3 oz. braider carrier springs on helical fibers The above-described prosthesis exhibited the load-strain behavior shown in FIG. 4 (the origin is drawn with reference to the untensioned state). The pros~hesis exhibits a tensile break point of 250 lbs. = 113 kg.
If the prosthesis is pretensioned to, for example, 10 l~s. tension (20% strain), it will exhibit an ~ e ~,o,~
~2;~6~
overall load modulus over a range of 37~ of the pretensioned length cf the prosthesis (equivalent to 44% of untensioned length~ of (250-10) lbs./(.37 unit of strain) = 295 kg./
(unit of strain). Above 20 lbs. load, the prosthesis will exhibit a substantially constant load modulus of (250-20) lbs./(0.31 unit of strain) = 340 kg./(unit of strain). No distinct yield point is observed prior to breakage.
EXAMPLE 2 0 Set 9 - Longitudinal fibers - 48 ends - Lycra Type 127 spandex-type polyurethane/polyether block copolymer coalesced multifilament (du Pont) - 280 denier Sets 11 and 13 - Helical fibers - same as in Example 1 5 Prosthesis configuration - same as in Example 1 except that circumference of tube is 19 mm.
Braiding angle - 48 Braiding ~)attern of sets 11 and 13 with respect to one another - 2-up and 2-down Densi.ty of -~indings of sets 11 and 13 -42 picks per inch Braiding tension - 20 to 25 g. on longitudinal fibers, 3 oz. braider carrier springs on helical fibers The above-described prosthesis exhibited the load-strain behavior shown in FIG. 5 (the origin is drawn with reference to the untensioned state). The prosthesis exhibits a tensile break point of 202 lbs. = 92 kg.
If the prosthesis is pretensioned to, for example, 7 Ibs. tension (40% strain), it will exhibit an overall load modulus over a range of 29~ of the pretensioned length of the prosthesis (equivalent to 40g of untensioned length) of (202-7) lbs./(.29 unit of strain) = 305 kg./
tunit of strain). Above 20 lbs. load, the prosthesis will exhibit a substantially constant load modulus of (202-20) lbs./(0.23 unit of strain) = 360 kg./(unit of strain). No dis~inct yield point is ob~erved prior to breakage.
Claims (20)
1. A prosthesis for use in repairing or replacing soft tissue comprising a triaxially-braided fabric element containing interwoven first, second and third sets of fibers, with the fibers of said first set being oriented in substantially the same direction, the fibers of said second and third sets being oriented at substantially the same acute braiding angle with respect to the fibers of said first set, and the fibers of one of said three sets having greater elasticity than the fibers of one or both of the other two of said three sets.
2. A prosthesis of claim 1 wherein the fibers of said first set have greater elasticity than the fibers of one or both of said second and third sets.
3. A prosthesis of claim 2 wherein the fibers of said first set have greater elasticity than the fibers of both of said second and third sets.
4. A prosthesis of claim 1 wherein said braiding angle is from about 10° to about 80°.
5. A prosthesis of claim 3 adapted for use in repairing or replacing ligament or tendon tissue, wherein said prosthesis has first and second opposed end portions adapted to be attached with said prosthesis in tension to the body of a patient, with said two end portions defining between them the longitudinal direction of the prosthesis, the fibers of said first set are oriented in substantially said longitudinal direction of the prosthesis, and the fibers of said second and third sets have greater yield strength and Young's modulus than the fibers of said first set.
6. A prosthesis of claim 5 wherein said braiding angle is from about 10° to about 80°, whereby the resistance of said prosthesis to longitudinal deforma-tion under longitudinal tensile loading decreases as said braiding angle is increased.
7. A prosthesis of claim 6 wherein the fibers of said second set are identical with the fibers of said third set.
8. A prosthesis of claim 7 wherein the fibers of said first set are made of a polyester/polyether block copolymer and the fibers of said second and third sets are made of polyethyleneterephthalate.
9. A prosthesis of claim 7 wherein the fibers of said first set are made of a polyurethane/polyether block copolymer and the fibers of said second and third sets are made of polyethyleneterephthalate.
10. A prosthesis of claim 7 wherein the fibers of said first set are made of a polyurethane/polyester block copolymer and the fibers of said second and third sets are made of polyethylenetsrephthalate.
11. A prosthesis of claim 5 wherein said element has the shape of a cylindrical tube, the fibers of said first set are oriented in the longitudinal direction of said tube and the fibers of said second and third sets are helically-disposed in the wall of said tube.
12. A prosthesis of claim 5 wherein said element has the shape of a flat elongated strip, the fibers of said first set are oriented in the longitudinal direction of said strip in essentially a single plane and the fibers of said second and third sets traverse said plane in a zig-zag manner.
13. A prosthesis of claim 5 wherein said fabric element includes means to visually indicate the degree of extension of said prosthesis in tension.
14. A prosthesis of claim 7 wherein said triaxially-braided fabric element contains interwoven first, second and third sets of synthetic polymeric fibers, said prosthesis exhibits a tensile break point of at least about 75 kg. and said prosthesis exhibits, after initial pretension, an overall load modulus of from about 200 kg./
(unit of strain) to about 600 kg./(unit of strain) over a range of substantially recoverable tensile elongation amounting to at least about 25 percent of the initial pretensioned length of the prosthesis.
(unit of strain) to about 600 kg./(unit of strain) over a range of substantially recoverable tensile elongation amounting to at least about 25 percent of the initial pretensioned length of the prosthesis.
15. A prosthesis of claim 1 wherein the fibers of said first set have lower elasticity than the fibers of one or both of said second and third sets.
16. A prosthesis of claim 15 wherein the fibers of said first set have lower elasticity than the fibers of both of said second and third sets.
17. A prosthesis of claim 3 adapted for use as a vascular prosthesis, wherein said element has the shape of a cylindrical tube, the fibers of said first set are oriented in the longitudinal direction of said tube and the fibers of said second and third sets are helically-disposed in the wall of said tube.
18. A prosthesis of claim 17 wherein said braiding angle is from about 10° to about 80°.
19. A prosthesis of claim 16 adapted for use as a heart valve prosthesis r wherein said prosthesis comprises:
a frame having a generally circular base defining the circumferential direction of the prosthesis and a plurality of spaced, generally parallel legs extending from said base; and a plurality of said fabric elements having the form of sheets and attached to said frame in such a manner that they function as heart valve leaflets during the operation of the valve, and wherein, in each of said fabric elements, the fibers of said first set are oriented in the circumferential direction of said valve when said valve is in the open position, the fibers of said second and third sets traverse said first set of fibers in a zig-zag manner, and the fibers of said first set have greater yield strength and Young's modulus than the fibers of said second and third sets.
a frame having a generally circular base defining the circumferential direction of the prosthesis and a plurality of spaced, generally parallel legs extending from said base; and a plurality of said fabric elements having the form of sheets and attached to said frame in such a manner that they function as heart valve leaflets during the operation of the valve, and wherein, in each of said fabric elements, the fibers of said first set are oriented in the circumferential direction of said valve when said valve is in the open position, the fibers of said second and third sets traverse said first set of fibers in a zig-zag manner, and the fibers of said first set have greater yield strength and Young's modulus than the fibers of said second and third sets.
20. A prosthesis of claim 19 wherein said braiding angle is from about 10° to about 80°.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US06/481,612 US4610688A (en) | 1983-04-04 | 1983-04-04 | Triaxially-braided fabric prosthesis |
US481,612 | 1983-04-04 |
Publications (1)
Publication Number | Publication Date |
---|---|
CA1220601A true CA1220601A (en) | 1987-04-21 |
Family
ID=23912661
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA000451068A Expired CA1220601A (en) | 1983-04-04 | 1984-04-02 | Triaxially-braided fabric prosthesis |
Country Status (14)
Country | Link |
---|---|
US (1) | US4610688A (en) |
EP (1) | EP0122744B1 (en) |
JP (1) | JPS59194738A (en) |
KR (1) | KR860001954B1 (en) |
AT (1) | ATE21816T1 (en) |
AU (1) | AU554461B2 (en) |
CA (1) | CA1220601A (en) |
DE (1) | DE3460597D1 (en) |
DK (1) | DK169500B1 (en) |
ES (1) | ES286681Y (en) |
IE (1) | IE55194B1 (en) |
IL (1) | IL71426A (en) |
MX (1) | MX159168A (en) |
ZA (1) | ZA842473B (en) |
Families Citing this family (289)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
SE445884B (en) * | 1982-04-30 | 1986-07-28 | Medinvent Sa | DEVICE FOR IMPLANTATION OF A RODFORM PROTECTION |
DE3566498D1 (en) * | 1984-03-01 | 1989-01-05 | Kanegafuchi Chemical Ind | Artificial vessel and process for preparing the same |
GB8414344D0 (en) * | 1984-06-05 | 1984-07-11 | Showell A W Sugicraft Ltd | Surgical element |
FR2569986B1 (en) * | 1984-09-11 | 1992-07-31 | Centre Nat Rech Scient | REPLACEMENT AND REPAIR PROSTHESES BASED ON POLYARYLAMIDE FIBERS AND MATERIALS OR PRODUCTS FOR SURGICAL USE |
US4997440A (en) * | 1985-04-25 | 1991-03-05 | American Cyanamid Company | Vascular graft with absorbable and nonabsorbable components |
US4871365A (en) * | 1985-04-25 | 1989-10-03 | American Cyanamid Company | Partially absorbable prosthetic tubular article having an external support |
US4923470A (en) * | 1985-04-25 | 1990-05-08 | American Cyanamid Company | Prosthetic tubular article made with four chemically distinct fibers |
US4708132A (en) * | 1986-01-24 | 1987-11-24 | Pfizer-Hospital Products Group, Inc. | Fixation device for a ligament or tendon prosthesis |
US4792336A (en) * | 1986-03-03 | 1988-12-20 | American Cyanamid Company | Flat braided ligament or tendon implant device having texturized yarns |
US4731084A (en) * | 1986-03-14 | 1988-03-15 | Richards Medical Company | Prosthetic ligament |
FR2598315B1 (en) * | 1986-05-07 | 1990-06-15 | Laboureau Jacques | ARTIFICIAL LIGAMENT IN IMPREGNATED SYNTHETIC TEXTILE AND ELASTIC RESIN COATING AND METHOD OF COATING |
FI81498C (en) * | 1987-01-13 | 1990-11-12 | Biocon Oy | SURGICAL MATERIAL OCH INSTRUMENT. |
US5192330A (en) * | 1987-01-20 | 1993-03-09 | Smith & Nephew Richards, Inc. | Orthopedic device of biocompatible polymer with oriented fiber reinforcement |
FR2617705B1 (en) * | 1987-07-09 | 1997-08-14 | Lemaire Marcel | ARTIFICIAL LIGAMENTS AND ARTICLES FOR CARRYING OUT THEM |
US4851000A (en) * | 1987-07-31 | 1989-07-25 | Pacific Biomedical Holdings, Ltd. | Bioprosthetic valve stent |
EP0375729A4 (en) * | 1987-08-19 | 1990-09-26 | E.I. Du Pont De Nemours And Company | Soft tissue prosthesis |
US5061283A (en) * | 1987-10-30 | 1991-10-29 | Pfizer Hospital Products Group, Inc. | Method for tendon and ligament repair |
DE3884743T2 (en) * | 1987-10-30 | 1994-01-27 | Howmedica | Device for restoring a tendon or ligament. |
EP0328401A1 (en) * | 1988-02-11 | 1989-08-16 | Unisearch Limited | Anastomosis augmentation device |
EP0331345A3 (en) * | 1988-03-02 | 1990-10-17 | Pfizer Hospital Products Group, Inc. | Triaxially woven fabric for heart valve |
US5092884A (en) * | 1988-03-24 | 1992-03-03 | American Cyanamid Company | Surgical composite structure having absorbable and nonabsorbable components |
US5197983A (en) * | 1988-04-19 | 1993-03-30 | W. L. Gore & Associates, Inc. | Ligament and tendon prosthesis |
US4917699A (en) * | 1988-05-16 | 1990-04-17 | Zimmer, Inc. | Prosthetic ligament |
US5026398A (en) * | 1988-07-01 | 1991-06-25 | The Minnesota Mining And Manufacturing Company | Abrasion resistant prosthetic device |
CH674928A5 (en) * | 1988-07-05 | 1990-08-15 | Experimentelle Chirurgie Lab | |
US6171338B1 (en) * | 1988-11-10 | 2001-01-09 | Biocon, Oy | Biodegradable surgical implants and devices |
FI85223C (en) * | 1988-11-10 | 1992-03-25 | Biocon Oy | BIODEGRADERANDE SURGICAL IMPLANT OCH MEDEL. |
US5147400A (en) * | 1989-05-10 | 1992-09-15 | United States Surgical Corporation | Connective tissue prosthesis |
US5217495A (en) * | 1989-05-10 | 1993-06-08 | United States Surgical Corporation | Synthetic semiabsorbable composite yarn |
US5376118A (en) * | 1989-05-10 | 1994-12-27 | United States Surgical Corporation | Support material for cell impregnation |
US4990158A (en) * | 1989-05-10 | 1991-02-05 | United States Surgical Corporation | Synthetic semiabsorbable tubular prosthesis |
US5141522A (en) * | 1990-02-06 | 1992-08-25 | American Cyanamid Company | Composite material having absorbable and non-absorbable components for use with mammalian tissue |
ATE120377T1 (en) * | 1990-02-08 | 1995-04-15 | Howmedica | INFLATABLE DILATATOR. |
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 |
DK0546021T3 (en) * | 1990-08-28 | 1996-03-18 | Meadox Medicals Inc | Self-supporting woven blood vessel graft |
CA2060635A1 (en) * | 1991-02-12 | 1992-08-13 | Keith D'alessio | Bioabsorbable medical implants |
FR2683716B1 (en) * | 1991-11-18 | 1994-01-21 | Jacques Bahuaud | REINFORCED GRAFT FOR LIGAMENTOPLASTY OF THE KNEE. |
JPH05161708A (en) * | 1991-12-18 | 1993-06-29 | Terumo Corp | Artificial blood vessel |
JP3335668B2 (en) * | 1992-06-12 | 2002-10-21 | テルモ株式会社 | Artificial blood vessel |
FR2699396B1 (en) * | 1992-12-17 | 1995-02-17 | Jean Frismand | Device for obtaining, adjusting and preserving a pre-stretched artificial ligament or tendon. |
US5456722A (en) * | 1993-01-06 | 1995-10-10 | Smith & Nephew Richards Inc. | Load bearing polymeric cable |
US5540703A (en) * | 1993-01-06 | 1996-07-30 | Smith & Nephew Richards Inc. | Knotted cable attachment apparatus formed of braided polymeric fibers |
ES2170093T3 (en) * | 1993-01-14 | 2002-08-01 | Meadox Medicals Inc | RADIAL EXPANDABLE TUBULAR PROTESIS. |
US5431676A (en) * | 1993-03-05 | 1995-07-11 | Innerdyne Medical, Inc. | Trocar system having expandable port |
AU7634094A (en) * | 1993-08-20 | 1995-03-21 | Smith & Nephew Richards Inc. | Self-reinforced ultra-high molecular weight polyethylene composites |
US5476508A (en) * | 1994-05-26 | 1995-12-19 | Tfx Medical | Stent with mutually interlocking filaments |
CA2206099C (en) * | 1994-12-02 | 2007-02-06 | Omeros Medical Systems, Inc. | Tendon and ligament repair system |
US6106556A (en) * | 1994-12-02 | 2000-08-22 | Omeros Medical Systems, Inc. | Tendon and ligament repair system |
BE1009277A3 (en) | 1995-04-12 | 1997-01-07 | Corvita Europ | Guardian self-expandable medical device introduced in cavite body, and method of preparation. |
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. |
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 |
US6348066B1 (en) * | 1995-11-07 | 2002-02-19 | Corvita Corporation | Modular endoluminal stent-grafts and methods for their use |
US5628788A (en) * | 1995-11-07 | 1997-05-13 | Corvita Corporation | Self-expanding endoluminal stent-graft |
US6929659B2 (en) | 1995-11-07 | 2005-08-16 | Scimed Life Systems, Inc. | Method of preventing the dislodgment of a stent-graft |
EP0955954B1 (en) * | 1996-01-05 | 2005-03-16 | Medtronic, Inc. | Expansible endoluminal prostheses |
US5843158A (en) * | 1996-01-05 | 1998-12-01 | Medtronic, Inc. | Limited expansion endoluminal prostheses and methods for their use |
CA2199890C (en) * | 1996-03-26 | 2002-02-05 | Leonard Pinchuk | Stents and stent-grafts having enhanced hoop strength and methods of making the same |
US5718159A (en) * | 1996-04-30 | 1998-02-17 | Schneider (Usa) Inc. | Process for manufacturing three-dimensional braided covered stent |
US6006134A (en) | 1998-04-30 | 1999-12-21 | Medtronic, Inc. | Method and device for electronically controlling the beating of a heart using venous electrical stimulation of nerve fibers |
US6592617B2 (en) * | 1996-04-30 | 2003-07-15 | Boston Scientific Scimed, Inc. | Three-dimensional braided covered stent |
US5824047A (en) * | 1996-10-11 | 1998-10-20 | C. R. Bard, Inc. | Vascular graft fabric |
US5952067A (en) * | 1996-12-02 | 1999-09-14 | A&P Technology, Inc. | Braided structure having uncrimped strands |
US6250193B1 (en) * | 1996-12-02 | 2001-06-26 | A & P Technology, Inc. | Braided structure with elastic bias strands |
US6015432A (en) * | 1998-02-25 | 2000-01-18 | Cordis Corporation | Wire reinforced vascular prosthesis |
US6494907B1 (en) | 1998-04-28 | 2002-12-17 | Intratherapeutics, Inc. | Braided stent |
US6245052B1 (en) | 1998-07-08 | 2001-06-12 | Innerdyne, Inc. | Methods, systems, and kits for implanting articles |
WO2000021454A1 (en) * | 1998-10-14 | 2000-04-20 | Rudo David N | Triaxial weave for reinforcing dental resins |
US6350277B1 (en) | 1999-01-15 | 2002-02-26 | Scimed Life Systems, Inc. | Stents with temporary retaining bands |
US6368346B1 (en) | 1999-06-03 | 2002-04-09 | American Medical Systems, Inc. | Bioresorbable stent |
US6197043B1 (en) * | 1999-08-18 | 2001-03-06 | James A. Davidson | Isoelastic suture material and device |
US8016877B2 (en) | 1999-11-17 | 2011-09-13 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
US8579966B2 (en) | 1999-11-17 | 2013-11-12 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
US7018406B2 (en) | 1999-11-17 | 2006-03-28 | Corevalve Sa | Prosthetic valve for transluminal delivery |
US6692513B2 (en) | 2000-06-30 | 2004-02-17 | Viacor, Inc. | Intravascular filter with debris entrapment mechanism |
LV12702B (en) | 2000-02-16 | 2001-10-20 | Viktorija Kancevica | Artery Prosthesis |
US6863696B2 (en) | 2000-02-16 | 2005-03-08 | Viktoria Kantsevitcha | Vascular prosthesis |
JP2004506469A (en) | 2000-08-18 | 2004-03-04 | アトリテック, インコーポレイテッド | Expandable implantable device for filtering blood flow from the atrial appendage |
US7229441B2 (en) * | 2001-02-28 | 2007-06-12 | Warsaw Orthopedic, Inc. | Flexible systems for spinal stabilization and fixation |
US6652585B2 (en) * | 2001-02-28 | 2003-11-25 | Sdgi Holdings, Inc. | Flexible spine stabilization system |
US6827743B2 (en) * | 2001-02-28 | 2004-12-07 | Sdgi Holdings, Inc. | Woven orthopedic implants |
US7344539B2 (en) * | 2001-03-30 | 2008-03-18 | Depuy Acromed, Inc. | Intervertebral connection system |
US20030069629A1 (en) * | 2001-06-01 | 2003-04-10 | Jadhav Balkrishna S. | Bioresorbable medical devices |
US8623077B2 (en) | 2001-06-29 | 2014-01-07 | Medtronic, Inc. | Apparatus for replacing a cardiac valve |
US7544206B2 (en) | 2001-06-29 | 2009-06-09 | Medtronic, Inc. | Method and apparatus for resecting and replacing an aortic valve |
US8771302B2 (en) | 2001-06-29 | 2014-07-08 | Medtronic, Inc. | Method and apparatus for resecting and replacing an aortic valve |
FR2826863B1 (en) | 2001-07-04 | 2003-09-26 | Jacques Seguin | ASSEMBLY FOR PLACING A PROSTHETIC VALVE IN A BODY CONDUIT |
FR2828091B1 (en) | 2001-07-31 | 2003-11-21 | Seguin Jacques | ASSEMBLY ALLOWING THE PLACEMENT OF A PROTHETIC VALVE IN A BODY DUCT |
DE60237899D1 (en) | 2001-08-01 | 2010-11-18 | Tyco Healthcare | DEVICE FOR OBTAINING PERCUTANEOUS ACCESS TO AND PROVIDING A MEDICAMENT AT AN OPERATING DESTINATION |
US7097659B2 (en) | 2001-09-07 | 2006-08-29 | Medtronic, Inc. | Fixation band for affixing a prosthetic heart valve to tissue |
US7029490B2 (en) | 2001-09-13 | 2006-04-18 | Arthrex, Inc. | High strength suture with coating and colored trace |
US8721713B2 (en) | 2002-04-23 | 2014-05-13 | Medtronic, Inc. | System for implanting a replacement valve |
FR2838631B1 (en) * | 2002-04-23 | 2004-12-24 | Engeneering And Technological | METHOD FOR PRODUCING AN AORTIC OR MITRAL HEART VALVE PROSTHESIS AND AORTIC OR MITRAL HEART VALVE PROSTHESIS THUS OBTAINED |
US7329268B2 (en) | 2002-07-02 | 2008-02-12 | Warsaw Orthopedic, Inc. | Expandable percutaneous sheath |
US7682392B2 (en) | 2002-10-30 | 2010-03-23 | Depuy Spine, Inc. | Regenerative implants for stabilizing the spine and devices for attachment of said implants |
DE60331463D1 (en) * | 2002-11-22 | 2010-04-08 | Tyco Healthcare | Medical system with pods |
US7479150B2 (en) | 2003-09-19 | 2009-01-20 | Tyco Healthcare Group Lp | Trocar insertion apparatus |
US9579194B2 (en) | 2003-10-06 | 2017-02-28 | Medtronic ATS Medical, Inc. | Anchoring structure with concave landing zone |
US7780692B2 (en) | 2003-12-05 | 2010-08-24 | Onset Medical Corporation | Expandable percutaneous sheath |
US9241735B2 (en) | 2003-12-05 | 2016-01-26 | Onset Medical Corporation | Expandable percutaneous sheath |
US7186265B2 (en) | 2003-12-10 | 2007-03-06 | Medtronic, Inc. | Prosthetic cardiac valves and systems and methods for implanting thereof |
US7445631B2 (en) | 2003-12-23 | 2008-11-04 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US20120041550A1 (en) | 2003-12-23 | 2012-02-16 | Sadra Medical, Inc. | Methods and Apparatus for Endovascular Heart Valve Replacement Comprising Tissue Grasping Elements |
US9005273B2 (en) | 2003-12-23 | 2015-04-14 | Sadra Medical, Inc. | Assessing the location and performance of replacement heart valves |
CN101947146B (en) | 2003-12-23 | 2014-08-06 | 萨德拉医学公司 | Relocatable heart valve |
US7329279B2 (en) | 2003-12-23 | 2008-02-12 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US11278398B2 (en) | 2003-12-23 | 2022-03-22 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US8840663B2 (en) | 2003-12-23 | 2014-09-23 | Sadra Medical, Inc. | Repositionable heart valve method |
US7824442B2 (en) | 2003-12-23 | 2010-11-02 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US20050137687A1 (en) | 2003-12-23 | 2005-06-23 | Sadra Medical | Heart valve anchor and method |
US8603160B2 (en) | 2003-12-23 | 2013-12-10 | Sadra Medical, Inc. | Method of using a retrievable heart valve anchor with a sheath |
US8182528B2 (en) | 2003-12-23 | 2012-05-22 | Sadra Medical, Inc. | Locking heart valve anchor |
US7824443B2 (en) | 2003-12-23 | 2010-11-02 | Sadra Medical, Inc. | Medical implant delivery and deployment tool |
US7780725B2 (en) | 2004-06-16 | 2010-08-24 | Sadra Medical, Inc. | Everting heart valve |
US7381219B2 (en) | 2003-12-23 | 2008-06-03 | Sadra Medical, Inc. | Low profile heart valve and delivery system |
US7959666B2 (en) | 2003-12-23 | 2011-06-14 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US8287584B2 (en) | 2005-11-14 | 2012-10-16 | Sadra Medical, Inc. | Medical implant deployment tool |
US8343213B2 (en) | 2003-12-23 | 2013-01-01 | Sadra Medical, Inc. | Leaflet engagement elements and methods for use thereof |
US20050137694A1 (en) | 2003-12-23 | 2005-06-23 | Haug Ulrich R. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US7748389B2 (en) | 2003-12-23 | 2010-07-06 | Sadra Medical, Inc. | Leaflet engagement elements and methods for use thereof |
US8579962B2 (en) | 2003-12-23 | 2013-11-12 | Sadra Medical, Inc. | Methods and apparatus for performing valvuloplasty |
US9526609B2 (en) | 2003-12-23 | 2016-12-27 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US8828078B2 (en) | 2003-12-23 | 2014-09-09 | Sadra Medical, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
ITTO20040135A1 (en) | 2004-03-03 | 2004-06-03 | Sorin Biomedica Cardio Spa | CARDIAC VALVE PROSTHESIS |
US20060025857A1 (en) | 2004-04-23 | 2006-02-02 | Bjarne Bergheim | Implantable prosthetic valve |
WO2006026397A2 (en) * | 2004-08-26 | 2006-03-09 | Stout Medical Group, L.P. | Sutures and methods of making the same |
US20060052867A1 (en) | 2004-09-07 | 2006-03-09 | Medtronic, Inc | Replacement prosthetic heart valve, system and method of implant |
US20060135981A1 (en) | 2004-09-09 | 2006-06-22 | Jay Lenker | Expandable transluminal sheath |
US7892203B2 (en) | 2004-09-09 | 2011-02-22 | Onset Medical Corporation | Expandable transluminal sheath |
US8562672B2 (en) | 2004-11-19 | 2013-10-22 | Medtronic, Inc. | Apparatus for treatment of cardiac valves and method of its manufacture |
DE102005003632A1 (en) | 2005-01-20 | 2006-08-17 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Catheter for the transvascular implantation of heart valve prostheses |
ITTO20050074A1 (en) | 2005-02-10 | 2006-08-11 | Sorin Biomedica Cardio Srl | CARDIAC VALVE PROSTHESIS |
US7962208B2 (en) | 2005-04-25 | 2011-06-14 | Cardiac Pacemakers, Inc. | Method and apparatus for pacing during revascularization |
US7914569B2 (en) | 2005-05-13 | 2011-03-29 | Medtronics Corevalve Llc | Heart valve prosthesis and methods of manufacture and use |
US8092481B2 (en) | 2005-06-03 | 2012-01-10 | Onset Medical Corporation | Expandable percutaneous sheath |
US7712606B2 (en) | 2005-09-13 | 2010-05-11 | Sadra Medical, Inc. | Two-part package for medical implant |
US20070078510A1 (en) | 2005-09-26 | 2007-04-05 | Ryan Timothy R | Prosthetic cardiac and venous valves |
US20070213813A1 (en) | 2005-12-22 | 2007-09-13 | Symetis Sa | Stent-valves for valve replacement and associated methods and systems for surgery |
US9078781B2 (en) | 2006-01-11 | 2015-07-14 | Medtronic, Inc. | Sterile cover for compressible stents used in percutaneous device delivery systems |
CN101415379B (en) | 2006-02-14 | 2012-06-20 | 萨德拉医学公司 | Systems for delivering a medical implant |
WO2007123658A1 (en) | 2006-03-28 | 2007-11-01 | Medtronic, Inc. | Prosthetic cardiac valve formed from pericardium material and methods of making same |
KR101433056B1 (en) | 2006-04-03 | 2014-08-22 | 페더럴-모걸 코오포레이숀 | End fray solution for textile structure |
US7625403B2 (en) | 2006-04-04 | 2009-12-01 | Medtronic Vascular, Inc. | Valved conduit designed for subsequent catheter delivered valve therapy |
US7524331B2 (en) | 2006-04-06 | 2009-04-28 | Medtronic Vascular, Inc. | Catheter delivered valve having a barrier to provide an enhanced seal |
US7740655B2 (en) | 2006-04-06 | 2010-06-22 | Medtronic Vascular, Inc. | Reinforced surgical conduit for implantation of a stented valve therein |
US7591848B2 (en) | 2006-04-06 | 2009-09-22 | Medtronic Vascular, Inc. | Riveted stent valve for percutaneous use |
US11304800B2 (en) | 2006-09-19 | 2022-04-19 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US8834564B2 (en) | 2006-09-19 | 2014-09-16 | Medtronic, Inc. | Sinus-engaging valve fixation member |
US8876894B2 (en) | 2006-09-19 | 2014-11-04 | Medtronic Ventor Technologies Ltd. | Leaflet-sensitive valve fixation member |
WO2008103280A2 (en) | 2007-02-16 | 2008-08-28 | Medtronic, Inc. | Delivery systems and methods of implantation for replacement prosthetic heart valves |
US8177834B2 (en) * | 2007-03-12 | 2012-05-15 | Cook Medical Technologies Llc | Woven fabric with shape memory element strands |
ES2744388T3 (en) | 2007-03-20 | 2020-02-24 | Allergan Inc | Tendon prostheses and manufacturing method |
US7896915B2 (en) | 2007-04-13 | 2011-03-01 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficiency |
FR2915087B1 (en) | 2007-04-20 | 2021-11-26 | Corevalve Inc | IMPLANT FOR TREATMENT OF A HEART VALVE, IN PARTICULAR OF A MITRAL VALVE, EQUIPMENT INCLUDING THIS IMPLANT AND MATERIAL FOR PLACING THIS IMPLANT. |
US8747458B2 (en) | 2007-08-20 | 2014-06-10 | Medtronic Ventor Technologies Ltd. | Stent loading tool and method for use thereof |
US9848981B2 (en) | 2007-10-12 | 2017-12-26 | Mayo Foundation For Medical Education And Research | Expandable valve prosthesis with sealing mechanism |
US8834552B2 (en) * | 2007-12-27 | 2014-09-16 | Cook Medical Technologies Llc | Stent graft having floating yarns |
FR2926452B1 (en) * | 2008-01-21 | 2011-03-11 | Jean Frismand | SURGICAL WIRE FOR RECONSTRUCTION IN THE FIELD OF SURGERY AND AESTHETIC MEDICINE |
EP2254512B1 (en) | 2008-01-24 | 2016-01-06 | Medtronic, Inc. | Markers for prosthetic heart valves |
US8628566B2 (en) | 2008-01-24 | 2014-01-14 | Medtronic, Inc. | Stents for prosthetic heart valves |
US8157852B2 (en) | 2008-01-24 | 2012-04-17 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US9149358B2 (en) | 2008-01-24 | 2015-10-06 | Medtronic, Inc. | Delivery systems for prosthetic heart valves |
US7972378B2 (en) | 2008-01-24 | 2011-07-05 | Medtronic, Inc. | Stents for prosthetic heart valves |
US9393115B2 (en) | 2008-01-24 | 2016-07-19 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US9044318B2 (en) | 2008-02-26 | 2015-06-02 | Jenavalve Technology Gmbh | Stent for the positioning and anchoring of a valvular prosthesis |
WO2011104269A1 (en) | 2008-02-26 | 2011-09-01 | Jenavalve Technology Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
EP3915525A1 (en) | 2008-02-28 | 2021-12-01 | Medtronic, Inc. | Prosthetic heart valve systems |
US8313525B2 (en) | 2008-03-18 | 2012-11-20 | Medtronic Ventor Technologies, Ltd. | Valve suturing and implantation procedures |
US8430927B2 (en) | 2008-04-08 | 2013-04-30 | Medtronic, Inc. | Multiple orifice implantable heart valve and methods of implantation |
US8312825B2 (en) | 2008-04-23 | 2012-11-20 | Medtronic, Inc. | Methods and apparatuses for assembly of a pericardial prosthetic heart valve |
US8696743B2 (en) | 2008-04-23 | 2014-04-15 | Medtronic, Inc. | Tissue attachment devices and methods for prosthetic heart valves |
US8840661B2 (en) * | 2008-05-16 | 2014-09-23 | Sorin Group Italia S.R.L. | Atraumatic prosthetic heart valve prosthesis |
WO2010031060A1 (en) | 2008-09-15 | 2010-03-18 | Medtronic Ventor Technologies Ltd. | Prosthetic heart valve having identifiers for aiding in radiographic positioning |
US8721714B2 (en) | 2008-09-17 | 2014-05-13 | Medtronic Corevalve Llc | Delivery system for deployment of medical devices |
DE102008048417A1 (en) * | 2008-09-23 | 2010-04-01 | Acandis Gmbh & Co. Kg | Medical device |
JP5607639B2 (en) | 2008-10-10 | 2014-10-15 | サドラ メディカル インコーポレイテッド | Medical devices and systems |
US8137398B2 (en) | 2008-10-13 | 2012-03-20 | Medtronic Ventor Technologies Ltd | Prosthetic valve having tapered tip when compressed for delivery |
US8986361B2 (en) | 2008-10-17 | 2015-03-24 | Medtronic Corevalve, Inc. | Delivery system for deployment of medical devices |
ES2551694T3 (en) | 2008-12-23 | 2015-11-23 | Sorin Group Italia S.R.L. | Expandable prosthetic valve with anchoring appendages |
EP2628465A1 (en) * | 2009-04-27 | 2013-08-21 | Sorin Group Italia S.r.l. | Prosthetic vascular conduit |
CA2762903C (en) * | 2009-05-22 | 2013-07-30 | Soft Tissue Regeneration, Inc. | Mechanically competent scaffold for ligament and tendon regeneration |
US8808369B2 (en) | 2009-10-05 | 2014-08-19 | Mayo Foundation For Medical Education And Research | Minimally invasive aortic valve replacement |
US20110190886A1 (en) * | 2010-01-29 | 2011-08-04 | Wisconsin Alumni Research Foundation | Braided tertiary nanofibrous structure for ligament, tendon, and muscle tissue implant |
US9226826B2 (en) | 2010-02-24 | 2016-01-05 | Medtronic, Inc. | Transcatheter valve structure and methods for valve delivery |
US9757132B2 (en) * | 2010-03-24 | 2017-09-12 | Biorez, Inc. | Mechanically competent scaffold for rotator cuff and tendon augmentation |
US8652204B2 (en) | 2010-04-01 | 2014-02-18 | Medtronic, Inc. | Transcatheter valve with torsion spring fixation and related systems and methods |
IT1400327B1 (en) | 2010-05-21 | 2013-05-24 | Sorin Biomedica Cardio Srl | SUPPORT DEVICE FOR VALVULAR PROSTHESIS AND CORRESPONDING CORRESPONDENT. |
CN103002833B (en) | 2010-05-25 | 2016-05-11 | 耶拿阀门科技公司 | Artificial heart valve and comprise artificial heart valve and support through conduit carry interior prosthese |
EP2588028A1 (en) * | 2010-06-29 | 2013-05-08 | University Of Virginia Patent Foundation | Anisotropic reinforcement and related method thereof |
EP2611476B1 (en) | 2010-09-02 | 2016-08-10 | Boston Scientific Scimed, Inc. | Coating process for drug delivery balloons using heat-induced rewrap memory |
CA2808673C (en) | 2010-09-10 | 2019-07-02 | Symetis Sa | Valve replacement devices, delivery device for a valve replacement device and method of production of a valve replacement device |
US20120172978A1 (en) * | 2011-01-05 | 2012-07-05 | Curia, Inc. | Prosthetic valves formed with isotropic filter screen leaflets |
EP2486894B1 (en) | 2011-02-14 | 2021-06-09 | Sorin Group Italia S.r.l. | Sutureless anchoring device for cardiac valve prostheses |
EP2486893B1 (en) | 2011-02-14 | 2017-07-05 | Sorin Group Italia S.r.l. | Sutureless anchoring device for cardiac valve prostheses |
WO2012127309A1 (en) | 2011-03-21 | 2012-09-27 | Ontorfano Matteo | Disk-based valve apparatus and method for the treatment of valve dysfunction |
EP2518208A3 (en) | 2011-04-27 | 2015-02-11 | Polteco Inc. | Abrasion resistant cords and ropes |
EP2520251A1 (en) | 2011-05-05 | 2012-11-07 | Symetis SA | Method and Apparatus for Compressing Stent-Valves |
WO2013009975A1 (en) | 2011-07-12 | 2013-01-17 | Boston Scientific Scimed, Inc. | Coupling system for medical devices |
CN104039271B (en) | 2011-07-29 | 2016-09-07 | 卡内基梅隆大学 | Artificial valve conduit and production method thereof for cardiac reconstruction operation |
US9056152B2 (en) | 2011-08-25 | 2015-06-16 | Boston Scientific Scimed, Inc. | Medical device with crystalline drug coating |
FR2980101A1 (en) * | 2011-09-20 | 2013-03-22 | Tornier Inc | REINFORCING STRIP FOR THE RESTORATION OF A SOFT TISSUE |
US9131926B2 (en) | 2011-11-10 | 2015-09-15 | Boston Scientific Scimed, Inc. | Direct connect flush system |
US8940014B2 (en) | 2011-11-15 | 2015-01-27 | Boston Scientific Scimed, Inc. | Bond between components of a medical device |
DE102011087404A1 (en) * | 2011-11-30 | 2013-06-06 | Mathys Ag Bettlach | Implantable system with elastic components |
US8951243B2 (en) | 2011-12-03 | 2015-02-10 | Boston Scientific Scimed, Inc. | Medical device handle |
US9277993B2 (en) | 2011-12-20 | 2016-03-08 | Boston Scientific Scimed, Inc. | Medical device delivery systems |
US9510945B2 (en) | 2011-12-20 | 2016-12-06 | Boston Scientific Scimed Inc. | Medical device handle |
EP2842517A1 (en) | 2011-12-29 | 2015-03-04 | Sorin Group Italia S.r.l. | A kit for implanting prosthetic vascular conduits |
US10172708B2 (en) | 2012-01-25 | 2019-01-08 | Boston Scientific Scimed, Inc. | Valve assembly with a bioabsorbable gasket and a replaceable valve implant |
KR20140138867A (en) | 2012-03-22 | 2014-12-04 | 티알비 케메디카 인터내셔널 에스.에이. | Method for repair of ligament or tendon |
US9883941B2 (en) | 2012-06-19 | 2018-02-06 | Boston Scientific Scimed, Inc. | Replacement heart valve |
EP3798226A1 (en) | 2013-02-01 | 2021-03-31 | Children's Medical Center Corporation | Collagen scaffolds |
AU2014225445B2 (en) * | 2013-03-08 | 2018-09-20 | Carnegie Mellon University | Expandable implantable conduit |
US9636222B2 (en) * | 2013-03-12 | 2017-05-02 | St. Jude Medical, Cardiology Division, Inc. | Paravalvular leak protection |
US9433489B2 (en) | 2013-03-12 | 2016-09-06 | Soft Tissue Regeneration, Inc. | Absorbable synthetic braided matrix for breast reconstruction and hernia repair |
US10561509B2 (en) | 2013-03-13 | 2020-02-18 | DePuy Synthes Products, Inc. | Braided stent with expansion ring and method of delivery |
US9585695B2 (en) | 2013-03-15 | 2017-03-07 | Woven Orthopedic Technologies, Llc | Surgical screw hole liner devices and related methods |
EP2991586A1 (en) | 2013-05-03 | 2016-03-09 | Medtronic Inc. | Valve delivery tool |
US9561103B2 (en) | 2013-07-17 | 2017-02-07 | Cephea Valve Technologies, Inc. | System and method for cardiac valve repair and replacement |
JP6563394B2 (en) | 2013-08-30 | 2019-08-21 | イェーナヴァルヴ テクノロジー インコーポレイテッド | Radially foldable frame for an artificial valve and method for manufacturing the frame |
US9949819B2 (en) * | 2014-02-13 | 2018-04-24 | Antonio Sambusseti | Non-absorbable tissue reconstruction device, in particular for tissues such as ligaments |
US10583003B2 (en) | 2014-05-06 | 2020-03-10 | Dsm Ip Assets B.V. | Method of making a prosthetic valve and valve obtained therewith |
EA033440B1 (en) | 2014-05-06 | 2019-10-31 | Dsm Ip Assets Bv | Prosthetic valve and method of making same |
WO2015169868A1 (en) | 2014-05-06 | 2015-11-12 | Dsm Ip Assets B.V. | Method of making a prosthetic valve and valve obtained therewith |
US10195025B2 (en) | 2014-05-12 | 2019-02-05 | Edwards Lifesciences Corporation | Prosthetic heart valve |
US8956394B1 (en) | 2014-08-05 | 2015-02-17 | Woven Orthopedic Technologies, Llc | Woven retention devices, systems and methods |
US9907593B2 (en) | 2014-08-05 | 2018-03-06 | Woven Orthopedic Technologies, Llc | Woven retention devices, systems and methods |
US10206796B2 (en) | 2014-08-27 | 2019-02-19 | DePuy Synthes Products, Inc. | Multi-strand implant with enhanced radiopacity |
US9943351B2 (en) | 2014-09-16 | 2018-04-17 | Woven Orthopedic Technologies, Llc | Woven retention devices, systems, packaging, and related methods |
USD740427S1 (en) | 2014-10-17 | 2015-10-06 | Woven Orthopedic Technologies, Llc | Orthopedic woven retention device |
US9901445B2 (en) | 2014-11-21 | 2018-02-27 | Boston Scientific Scimed, Inc. | Valve locking mechanism |
US9517062B2 (en) | 2014-12-03 | 2016-12-13 | Smith & Nephew, Inc. | Closed loop suture for anchoring tissue grafts |
WO2016093877A1 (en) | 2014-12-09 | 2016-06-16 | Cephea Valve Technologies, Inc. | Replacement cardiac valves and methods of use and manufacture |
WO2016115375A1 (en) | 2015-01-16 | 2016-07-21 | Boston Scientific Scimed, Inc. | Displacement based lock and release mechanism |
US9861477B2 (en) | 2015-01-26 | 2018-01-09 | Boston Scientific Scimed Inc. | Prosthetic heart valve square leaflet-leaflet stitch |
WO2016126524A1 (en) | 2015-02-03 | 2016-08-11 | Boston Scientific Scimed, Inc. | Prosthetic heart valve having tubular seal |
US9788942B2 (en) | 2015-02-03 | 2017-10-17 | Boston Scientific Scimed Inc. | Prosthetic heart valve having tubular seal |
US10925716B2 (en) | 2015-02-25 | 2021-02-23 | Smith & Nephew, Inc. | Closed loop suture for anchoring tissue grafts |
US10285809B2 (en) | 2015-03-06 | 2019-05-14 | Boston Scientific Scimed Inc. | TAVI anchoring assist device |
US10426617B2 (en) | 2015-03-06 | 2019-10-01 | Boston Scientific Scimed, Inc. | Low profile valve locking mechanism and commissure assembly |
US10080652B2 (en) | 2015-03-13 | 2018-09-25 | Boston Scientific Scimed, Inc. | Prosthetic heart valve having an improved tubular seal |
CN107530168B (en) | 2015-05-01 | 2020-06-09 | 耶拿阀门科技股份有限公司 | Device and method with reduced pacemaker ratio in heart valve replacement |
EP3294220B1 (en) | 2015-05-14 | 2023-12-06 | Cephea Valve Technologies, Inc. | Cardiac valve delivery devices and systems |
EP3294221B1 (en) | 2015-05-14 | 2024-03-06 | Cephea Valve Technologies, Inc. | Replacement mitral valves |
WO2018136959A1 (en) | 2017-01-23 | 2018-07-26 | Cephea Valve Technologies, Inc. | Replacement mitral valves |
WO2017004377A1 (en) | 2015-07-02 | 2017-01-05 | Boston Scientific Scimed, Inc. | Adjustable nosecone |
US10195392B2 (en) | 2015-07-02 | 2019-02-05 | Boston Scientific Scimed, Inc. | Clip-on catheter |
WO2017024277A1 (en) | 2015-08-05 | 2017-02-09 | Woven Orthopedic Technologies, Llc | Tapping devices, systems and methods for use in bone tissue |
US10179041B2 (en) | 2015-08-12 | 2019-01-15 | Boston Scientific Scimed Icn. | Pinless release mechanism |
US10136991B2 (en) | 2015-08-12 | 2018-11-27 | Boston Scientific Scimed Inc. | Replacement heart valve implant |
US10779940B2 (en) | 2015-09-03 | 2020-09-22 | Boston Scientific Scimed, Inc. | Medical device handle |
US10342660B2 (en) | 2016-02-02 | 2019-07-09 | Boston Scientific Inc. | Tensioned sheathing aids |
EP3432940A2 (en) | 2016-03-25 | 2019-01-30 | Biorez, Inc. | Complex braided scaffolds for improved tissue regeneration |
US10245136B2 (en) | 2016-05-13 | 2019-04-02 | Boston Scientific Scimed Inc. | Containment vessel with implant sheathing guide |
US10583005B2 (en) | 2016-05-13 | 2020-03-10 | Boston Scientific Scimed, Inc. | Medical device handle |
EP4183371A1 (en) | 2016-05-13 | 2023-05-24 | JenaValve Technology, Inc. | Heart valve prosthesis delivery system and method for delivery of heart valve prosthesis with introducer sheath and loading system |
US10201416B2 (en) | 2016-05-16 | 2019-02-12 | Boston Scientific Scimed, Inc. | Replacement heart valve implant with invertible leaflets |
US11331187B2 (en) | 2016-06-17 | 2022-05-17 | Cephea Valve Technologies, Inc. | Cardiac valve delivery devices and systems |
US10076428B2 (en) | 2016-08-25 | 2018-09-18 | DePuy Synthes Products, Inc. | Expansion ring for a braided stent |
US10292851B2 (en) | 2016-09-30 | 2019-05-21 | DePuy Synthes Products, Inc. | Self-expanding device delivery apparatus with dual function bump |
US10182927B2 (en) * | 2016-10-21 | 2019-01-22 | DePuy Synthes Products, Inc. | Expansion ring for a braided stent |
EP3551105A4 (en) | 2016-12-09 | 2020-07-29 | Woven Orthopedic Technologies, LLC | Retention devices, lattices and related systems and methods |
AU2018203053B2 (en) | 2017-01-23 | 2020-03-05 | Cephea Valve Technologies, Inc. | Replacement mitral valves |
JP7094965B2 (en) | 2017-01-27 | 2022-07-04 | イエナバルブ テクノロジー インク | Heart valve imitation |
WO2018226915A1 (en) | 2017-06-08 | 2018-12-13 | Boston Scientific Scimed, Inc. | Heart valve implant commissure support structure |
CN111163729B (en) | 2017-08-01 | 2022-03-29 | 波士顿科学国际有限公司 | Medical implant locking mechanism |
US10939996B2 (en) | 2017-08-16 | 2021-03-09 | Boston Scientific Scimed, Inc. | Replacement heart valve commissure assembly |
GB201717885D0 (en) * | 2017-10-31 | 2017-12-13 | Hothouse Medical Ltd | Prothesis and method of manufacture |
FR3073391B1 (en) * | 2017-11-10 | 2021-08-27 | Cousin Biotech | FLAT SOFT TEXTILE LONG LINE ELEMENT INCLUDING A DEVICE FOR IDENTIFYING ITS FACES A AND B OPPOSITE |
JP7055882B2 (en) | 2018-01-19 | 2022-04-18 | ボストン サイエンティフィック サイムド,インコーポレイテッド | Guidance mode indwelling sensor for transcatheter valve system |
US11246625B2 (en) | 2018-01-19 | 2022-02-15 | Boston Scientific Scimed, Inc. | Medical device delivery system with feedback loop |
US11147668B2 (en) | 2018-02-07 | 2021-10-19 | Boston Scientific Scimed, Inc. | Medical device delivery system with alignment feature |
WO2019165394A1 (en) | 2018-02-26 | 2019-08-29 | Boston Scientific Scimed, Inc. | Embedded radiopaque marker in adaptive seal |
CN112399836A (en) | 2018-05-15 | 2021-02-23 | 波士顿科学国际有限公司 | Replacement heart valve commissure assemblies |
WO2019224577A1 (en) | 2018-05-23 | 2019-11-28 | Sorin Group Italia S.R.L. | A cardiac valve prosthesis |
US11241310B2 (en) | 2018-06-13 | 2022-02-08 | Boston Scientific Scimed, Inc. | Replacement heart valve delivery device |
AU2019204522A1 (en) | 2018-07-30 | 2020-02-13 | DePuy Synthes Products, Inc. | Systems and methods of manufacturing and using an expansion ring |
US10278848B1 (en) | 2018-08-06 | 2019-05-07 | DePuy Synthes Products, Inc. | Stent delivery with expansion assisting delivery wire |
US10456280B1 (en) | 2018-08-06 | 2019-10-29 | DePuy Synthes Products, Inc. | Systems and methods of using a braided implant |
WO2020123486A1 (en) | 2018-12-10 | 2020-06-18 | Boston Scientific Scimed, Inc. | Medical device delivery system including a resistance member |
CA3120097C (en) | 2018-12-13 | 2023-07-04 | Abbott Laboratories | Fabric material for medical devices |
US20210121290A1 (en) | 2019-10-24 | 2021-04-29 | Abbott Laboratories | Sheet material for medical devices |
US11547557B2 (en) | 2018-12-13 | 2023-01-10 | Abbott Laboratories | Stabilized fabric material for medical devices |
US11039944B2 (en) | 2018-12-27 | 2021-06-22 | DePuy Synthes Products, Inc. | Braided stent system with one or more expansion rings |
US11439504B2 (en) | 2019-05-10 | 2022-09-13 | Boston Scientific Scimed, Inc. | Replacement heart valve with improved cusp washout and reduced loading |
EP4164551A1 (en) | 2020-06-11 | 2023-04-19 | Abbott Laboratories | Fabric material for medical devices |
EP4146126A1 (en) * | 2020-06-11 | 2023-03-15 | Edwards Lifesciences Corporation | Stiff braid member for prosthetic valve delivery apparatus |
US20220265423A1 (en) | 2021-02-24 | 2022-08-25 | St. Jude Medical, Cardiology Division, Inc. | Leaflet Attachment To Prosthetic Heart Valve |
CN113878955B (en) * | 2021-09-27 | 2024-02-23 | 宁波健世科技股份有限公司 | Multilayer composite bionic polymer leaflet and manufacturing method thereof |
Family Cites Families (24)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3176316A (en) * | 1963-01-07 | 1965-04-06 | Bruce R Bodell | Plastic prosthetic tendon |
US3431814A (en) * | 1967-10-25 | 1969-03-11 | Stevens & Co Inc J P | Soft-feel,long-stretch,elastic braid |
US3613120A (en) * | 1969-10-21 | 1971-10-19 | Research Corp | Flexor tendon prosthesis |
US4340091A (en) * | 1975-05-07 | 1982-07-20 | Albany International Corp. | Elastomeric sheet materials for heart valve and other prosthetic implants |
US4192020A (en) * | 1975-05-07 | 1980-03-11 | Washington University | Heart valve prosthesis |
US4191218A (en) * | 1975-05-07 | 1980-03-04 | Albany International Corp. | Fabrics for heart valve and vascular prostheses and methods of fabricating same |
US4127902A (en) * | 1976-06-07 | 1978-12-05 | Homsy Charles A | Structure suitable for in vivo implantation |
US4297749A (en) * | 1977-04-25 | 1981-11-03 | Albany International Corp. | Heart valve prosthesis |
US4149277A (en) * | 1977-06-22 | 1979-04-17 | General Atomic Company | Artificial tendon prostheses |
JPS5842822B2 (en) * | 1977-10-15 | 1983-09-22 | 株式会社カクイチ製作所 | Method for manufacturing a foldable synthetic resin hose with embedded reinforcing material |
US4209859A (en) * | 1978-03-29 | 1980-07-01 | Meadox Medicals, Inc. | Ligament and tendon prosthesis of polyethylene terephthalate and method of preparing same |
US4246660A (en) * | 1978-12-26 | 1981-01-27 | Queen's University At Kingston | Artificial ligament |
US4380483A (en) * | 1979-01-15 | 1983-04-19 | Celanese Corporation | Process for forming improved carbon fiber reinforced composite coil spring |
US4329743A (en) * | 1979-04-27 | 1982-05-18 | College Of Medicine And Dentistry Of New Jersey | Bio-absorbable composite tissue scaffold |
CA1112401A (en) * | 1979-05-24 | 1981-11-17 | Roland Dore | Deformable high energy storage tension spring |
US4255820A (en) * | 1979-07-24 | 1981-03-17 | Rothermel Joel E | Artificial ligaments |
US4384022A (en) * | 1980-05-09 | 1983-05-17 | Minnesota Mining And Manufacturing Co. | Filamentary structure |
CH644748A5 (en) * | 1980-06-03 | 1984-08-31 | Sulzer Ag | STRING AND / OR TAPE REPLACEMENT MATERIAL. |
US4469101A (en) * | 1980-10-23 | 1984-09-04 | Battelle Memorial Institute | Suture device |
US4455690A (en) * | 1980-11-06 | 1984-06-26 | Homsy Charles A | Structure for in vivo implanation |
WO1982001647A1 (en) * | 1980-11-17 | 1982-05-27 | Robert L Kaster | Vascular graft |
US4416028A (en) * | 1981-01-22 | 1983-11-22 | Ingvar Eriksson | Blood vessel prosthesis |
CH651463A5 (en) * | 1981-06-24 | 1985-09-30 | Sulzer Ag | STRING AND / OR TAPE REPLACEMENT. |
US4467478A (en) * | 1982-09-20 | 1984-08-28 | Jurgutis John A | Human ligament replacement |
-
1983
- 1983-04-04 US US06/481,612 patent/US4610688A/en not_active Expired - Lifetime
-
1984
- 1984-03-29 EP EP84302134A patent/EP0122744B1/en not_active Expired
- 1984-03-29 AT AT84302134T patent/ATE21816T1/en not_active IP Right Cessation
- 1984-03-29 DE DE8484302134T patent/DE3460597D1/en not_active Expired
- 1984-04-02 IL IL71426A patent/IL71426A/en not_active IP Right Cessation
- 1984-04-02 CA CA000451068A patent/CA1220601A/en not_active Expired
- 1984-04-03 DK DK176984A patent/DK169500B1/en not_active IP Right Cessation
- 1984-04-03 AU AU26365/84A patent/AU554461B2/en not_active Ceased
- 1984-04-03 KR KR1019840001750A patent/KR860001954B1/en not_active IP Right Cessation
- 1984-04-03 JP JP59066618A patent/JPS59194738A/en active Granted
- 1984-04-03 ES ES1984286681U patent/ES286681Y/en not_active Expired
- 1984-04-03 ZA ZA842473A patent/ZA842473B/en unknown
- 1984-04-03 MX MX200897A patent/MX159168A/en unknown
- 1984-04-03 IE IE822/84A patent/IE55194B1/en not_active IP Right Cessation
Also Published As
Publication number | Publication date |
---|---|
DK176984A (en) | 1984-10-05 |
ATE21816T1 (en) | 1986-09-15 |
DE3460597D1 (en) | 1986-10-09 |
EP0122744B1 (en) | 1986-09-03 |
AU554461B2 (en) | 1986-08-21 |
ES286681U (en) | 1986-04-16 |
EP0122744A1 (en) | 1984-10-24 |
US4610688A (en) | 1986-09-09 |
JPS6140420B2 (en) | 1986-09-09 |
JPS59194738A (en) | 1984-11-05 |
KR860001954B1 (en) | 1986-11-05 |
AU2636584A (en) | 1984-10-11 |
IE840822L (en) | 1984-10-04 |
IL71426A (en) | 1988-06-30 |
KR840008274A (en) | 1984-12-14 |
MX159168A (en) | 1989-04-26 |
ZA842473B (en) | 1985-11-27 |
IE55194B1 (en) | 1990-06-20 |
DK169500B1 (en) | 1994-11-14 |
IL71426A0 (en) | 1984-07-31 |
DK176984D0 (en) | 1984-04-03 |
ES286681Y (en) | 1986-12-01 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA1220601A (en) | Triaxially-braided fabric prosthesis | |
US4834755A (en) | Triaxially-braided fabric prosthesis | |
US4728329A (en) | Prosthetic band | |
CA1251302A (en) | Prosthetic ligament | |
US4642119A (en) | Connective tissue prosthesis | |
EP0375729A4 (en) | Soft tissue prosthesis | |
US4773910A (en) | Permanent ligament prosthesis | |
US4255820A (en) | Artificial ligaments | |
US8197537B2 (en) | Implantable textile prostheses having PTFE cold drawn yarns | |
JPH0224542B2 (en) | ||
US4795466A (en) | Artificial crucial ligament for a knee joint | |
EP0485986A1 (en) | Connective tissue prosthesis | |
WO2016126511A2 (en) | Prosthetic heart valve having tubular seal | |
EP0502989A1 (en) | Prosthetic anterior cruciate ligament design | |
WO2016126509A1 (en) | Prosthetic heart valve having notched leaflet | |
JP2012507319A (en) | Tubular implantable cord | |
JP2002532156A (en) | Implant for implantation into a human or animal containing a flexible thread-like element | |
AU2021293512A1 (en) | Suture device | |
WO1993006790A2 (en) | Tissue augmentation device and method |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
MKEX | Expiry |