US3142067A - Synthetic vascular implants - Google Patents

Synthetic vascular implants Download PDF

Info

Publication number
US3142067A
US3142067A US8986261A US3142067A US 3142067 A US3142067 A US 3142067A US 8986261 A US8986261 A US 8986261A US 3142067 A US3142067 A US 3142067A
Authority
US
Grant status
Grant
Patent type
Prior art keywords
implant
fabric
tubular
mandrel
stem
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
Inventor
William J Liebig
Original Assignee
William J Liebig
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Grant date

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2/00Filters 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
    • A61F2/02Prostheses implantable into the body
    • A61F2/04Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06Blood vessels
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2/00Filters 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
    • A61F2/02Prostheses implantable into the body
    • A61F2/04Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06Blood vessels
    • A61F2002/065Y-shaped blood vessels

Description

W. J. LIEBIG July 28, 1964 SYNTHETIC VASCULAR IMPLANTS Original Filed Nov. 21, 1958 WILLIAM J. LIEBIG ATTORN EYS 3,142,067 SYNTHETEC VASCULAR IMPLANTS William J. Liehig, Martha Road, Harrington Parlr, NJ. Original application Nov. 21, 1958, Ser. No. 775,522, now Patent No. 3,086,560, dated July 9, 1863. Divided and this application Feb. 16, 1961, Ser. No. 89,862

3 Qlairns. (Cl. 31)

This invention concerns vascular prostheses and aims to provide for such devices as improved flexible and resilient self-supporting tubular wall structure which affords a normal open form for the prosthetic tube defined there by and in which form it is supple and plaint as to flexure capacity, is extensible and contractible elastically lengthwise, and has the property of automatic return to the open form with little or no remnant deformation upon release of bending, compressive or other distorting stress.

This application is a division of my copending application Serial No. 775,522, filed November 21, 1958, now

Patent No. 3,096,560.

The invention is more particularly pertinent to nonsewn tubular woven synthetic vascular implants such as fully disclosed and claimed in my copending application Serial No. 653,562, filed April 18, 1957, now Patent No. 2,978,787. It generally improves thereon by correlating with the all-woven basic tubular body formation thereof a determined lateral and circumferential wall modification presenting a smooth interior and a finely folded exterior structure herein sometimes termed micro-crimping, having reference both to the method and to the resultant forerally to that of FIG. 1;

FIG. 4 represents a further stage like that of FIG. 2;

FIG. 5 shows separately a mandrel such as used for bifurcate implants, with legs thereof demounted;

FIG. 6 on a smaller scale shows the mandrel of FIG. 5 assembled;

FIG. 7 is an elevational view of a length of implant of the invention, such as that of FIGS. 2 to 4, with a portion sectioned to show the generally smooth internal wall surface as presented by the multiplicity of narrow closeabutted woven fabric rings thereat; and

FIG. 8 is a partly diagrammatic perspective of an end portion of an implant fabric blank unit such as of FIGS. 1 and 3 before micro-crimping.

Referring to the drawings in more detail the vascular prostheses or implants of this invention are basically fabricated by weaving them in flat tubular form upon a specially modified Jacquard loom so that a plurality of fine dense fabric plies are interwoven along longitudinal integral union zones, the resultant continuous tubular nonsewn bodies being composed of multi-filament circumferential warp and longitudinal filling strands.

These implants may have various overall forms of which two main categories are herein illustrated. FIGS. 1 and 2 show an implant of the single-tube, simple or straight-line form, designated as a whole at 10. FIGS.

3 and 4 show an important divided, bifurcate or Y-form, indicated as a whole at 20.

An implant 18, at an intermediate stage following severance from the larger fabric blank that comes from the loom, is seen at the right in FIG. 1, in more or less flat- 3,l42,%7 Patented July 28, 1964 tened or partly open condition, as indicated at 10A and similarly at 20A in FIG. 3; see also FIG. 8. It comprises superposed woven fabric plies 11, 11' integrally joined in longitudinal non-sewn flange-like seams or seal-formations 12 along diametrically opposite longitudinal portions. These axis-paralleling unions or seal-formations 12 are composite non-sewn integral fabric structures interwoven as part of the tubular implant body as a whole. Each contains a dual-ply fabric area demarked from the adjoined main tubular portion by sealing lines of union where the constituent warp is cross-shedded, as at S, S and 8", FIG. 8.

As noted, an implant unit such as 10 of FIGS. 1 and 2 is severed from others initially in the same plural-ply woven fabric web. The severance is along a crossshedded line of ply union such as S of FIG. 8 spaced by at least one other such union line from the adjoined main tubular area of the fabric; see such lines S and S in FIG. 8. Along the severance line S the component synthetic multi-filament yarns are heat-sealed as by a heated severing instrument to afford a fused seal in addition to the one or more in-woven lines. of union contained in the entirety of each of the respective integral longitudinal unions or seal formations 12. The foregoing description of the non-sewn woven tubular fabric along with the present drawings is adequate for the purposes of this application and is as disclosed in greater detail in my mentioned copending application.

As in said earlier application the woven tubular unit blanks as at 10A and 20A are composed of fine-denier multi-filarnent synthetic Warp and filling yarns of materials selected for desired vascular implant properties. These include compatability with human tissue along with wettability for blood such as to promote the starting of clotting and the attendant growth of a layer of collagen on the wall of the prosthetic tubing after implantation, and further include strength, flexibility and resilience, appropriate water-absorptivity and capacity to withstand sterilization. The multi-filament yarn found most satisfactory to date is a terephthalic acid-ethylene glycol ester as commercially produced by Du Pont de Nemours Co. under the trademark Dacron. Some of the desired characteristics are present in other commercially available synthetic fibres including the long-chain polyamide type of the nylon class, those of the tetrafluoroethylene type known under the trademark Teflon, also the type commercially designated as Orlon. In the presently preferred example the weaving is accomplished with a 34-filament Dacron yarn of approximately 70 denier as for example that known commercially as Du Pont Type 5 6 (formerly called 5600), received from the manufacturer with zero twist and preparatorily to weaving given a relatively soft twist as for example about a 9 to 12 turn left or Z twist for warp and about a 5 turn left Z or right 8 twist for filling.

In accordance with the invention, wherein the porosity of the fabric is a function both of the size and of the multi-filament nature of the yarns as well as of the close proximity of the yarns as laid in the weaving operation, an extremely close or dense weave of the selected yarns is needed for the relatively low order of porosity here concerned, desirably not less than 16 nor greater than about 25 to 30 porosity in terms of cubic feet of air per minute through a square foot of the fabric at a pressure of 1.26 in. of water. Utilizing as preferred example a 70 denier 34-filament Dacron yarn, suitable fabric fineness, density and porosity is obtained when each cloth or ply of the dual-layer fabric has a count in the order of 150 or more warp ends by or more filling picks per inch in a plain or so-called taffeta weave, the loom generally employing in the two cloths or plies a total of over 300 warp ends by 200 picks per inch, in one example 168 warp ends by 108 filling picks per inch. Further by way of specific example but without limitation thereto a specially modified Jacquard loom in one case .of actual practice weaves a 50-inch web incorporating a sheet of 15,360 Warp ends appropriately divided for shedding into two warp 'sets, the integral unions of the fabric plies as above mentioned being accomplished by causing the respective warp sets to cross over as appropriate for the shape and dimension of the particular tubular implant desired.

On the accompanying drawing the multi-filament warp yarns, extending circumferentially of the tube are designatedat w and the similar filling yarns, lengthwise of the tube, at f, FIGS. 1, 3, 7 and 8.

The resultant woven integrally sealed non-sewn tubular elements or implant units at A and A hereof, following dofling of the fabric web from the loom and severance of the individual implant units as already described are under the present invention accorded the further processing whereby the finished tubular products incorporate markedly improved characteristics as to lateral flexibility and resilience and axial elastic extension coupled with the capacity of self-support in and self-return to open tubular form.

In such processing I employ forming and ironing mandrels of generally cylindrical rod form and of metal or other material adapted for heating and free of objectionable chemical or contaminant effect-on the tubular fabric blanks received thereon. Preferred materials include stainless steel and chemically pure anodized aluminum.

For the single-tube form of FIGS. 1 and 2 the mandrel 30 is a straight rod of circular cross-section having at one or both ends a rounded nose as at 31. Each such mandrel 30 is accurately scaled to an outer diameter closely matching the inner diameter for the particular size of implant in the finished inflated or open status. The mandrels, which are provided with a smooth hard outer surface, accordingly are made of lumen-filling dimension with respect to the tubular implant units. Typical examples for the straight or single-tube implants of FIGS. 1 and -2 are as follows:

Straight Tubes Open Diameter, mm.

The values in the right-hand column under Open Diameter are the lumen size of the ready-for-use implant in relaxed status. The mandrel diameter at room temperature is closely scaled to the lumen of the particular implant.

Having furnished and selected the appropriate mandrel 30 the woven tubular implant blank 10A preferably moistened in a water bath is passed and collected in a moist state onto the mandrel received snugly within it. The fabric blank is axially compressed on the mandrel 30 so that it is condensed to approximately of the original length of the blank. This is accomplished mechanically or by by hand, the foremost end of the blank being passed along over the mandrel to a distance from the receiving end thereof at least equal to the final condensed length of the implant. In FIG. 1 the blank 10A is shown in progression onto the mandrel and in the course of being compressed. In FIG. 2 the compressive approximate 4:1 length reduction has been completed.

This operation of compressing the moistened fabric blank onto the mandrel creates at the same time a longitudinal array of minute circumferential pleats or crimps 15 upon the tubular fabric wall, shown on an enlarged scale in FIG. 7 and seen more or less diagrammatically in each of FIGS. 1 to 4. These pleats 15 are wholly external to the inner circumferential surface of the tubular implant as compelled by the filling diameter of the forming mandrel 30. Under the stated 4 to l compressive axial reduction the two radial walls of each individual pleat or crimp 15 are approached to each other into largely closed or random touching proximate contiguity, particularly at the basal portions. Also in the longitudinal array as a whole the multiplicity of minute pleats or crimps 15 which I term micro-crimping are closely compacted one with the next in somewhat re-entrant or partially interfitting relation in a closed rank or stack.

Noting particularly FIG. 7, the short pleats or crimps 15 of the multiplicity thereof are of uneven outward radial extent and individually vary in cross-sectional contour. While the outward radial extent of the microcrimping is a function of the diameter of the implant tube and of the mandrel, increasing with the tube diameter, the exact shaping thereof is random and without deliberate mechanical or measured distribution into a certain number of crimps per inch or into absolute regularity in radial extent and area. Otherwise stated, the micro-crimping is that resultant from and characterized by axial compressive reduction of the tubular fabric blank in a moist state to approximately 25% of the original length in conjunction with installation upon a smooth hard-surfaced incompressible mandrel of full scale or filling size equivalent to the desired lumen for the particular tubular implant product.

Further, in the described micro-crimping procedure the plural-ply radially projective longitudinal seal formations 12 automatically accommodate themselves to the close fine pleating 15 of the tube body. They likewise assume a random compressed, pleated or ruffled form with the crests of the pleats some to one side and some to the other side of the original longitudinal line of sealing union along the tube body, in oppositely offset relation with respect to that line, in a manner resembling a positive and negative curve along a zero reference line. Also the fabric of the seal formations 12 is in major part external to the crests of the body pleats 15. Thus these seal formations 12 conform themselves to the same proportionate approximate 4 to 1 length reduction as for the tubular body portion, noting particularly the elevational portion of FIG. 7. These micro-crimped seal zones 12 while importing little or no decrease in flexibility, lateral resilience or axial elasticity for the resulting tubular implant as a whole, contribute to the overall capacity of the implant for self-maintenance in a normal open condition and for return thereto on removal of deforming I force.

Referring again to FIG. 7 showing a completed implant the interior thereof presents a cylindrical surface defined by a multiplicity of uniform-diametered inwardly smooth rings 16 of like number as that of the pleats or crimps 1'5 and spanning between them in mutually touching side by side relation over the entire longitudinal extent of the implant tube in the normal or relaxed state of the final product. In completing the processing these internal wall-defining rings 16 are in effect internally ironed to present a smooth cylindrical wall surface wholly uninterrupted circumferentially and being effectively closed or continuous longitudinally in the normal unstressed status of the tubular device.

With the tubular fabric unit installed in a moist state and fully compressed to ultimate reduced length as in FIG. 2 or 4, the carrying mandrel 30 or is inserted into an oven where it is located over a water bath and is heated to a temperature determinately below the melting point of the component synthetic yarns. In the preferred instance of Dacron for example, having a melting point of 480 F., the oven temperature is held to not exceeding about 425 F., the fabric thus being subjected to a slightly moist heat over the water bath in the oven. Under this treatment the metallic mandrel 30 tends to expand and accordingly imparts to the inner interpleat rings 16 a further smoothing or ironing action and resultant substantially uniform cylindrical inner surface for the device as a whole. This ironing heat and moisture treatment is of short duration accurately timed for optimum effect. In practice the best timing is found to be approximately 15 minutes, any variation therefrom desirably being not more than about one and one-half minutes plus or minus.

At the end of the controlled heating period the mandrel and micro-crimped implant unit thereon are removed from the oven and placed into a relatively cool water bath at approximately 70 F., or substantially room temperature for a cooling period of about five minutes. This cools and shrinks the mandrel and is believed to have some beneficial adjustive or relaxing effect upon the component synthetic yarns and the multi-filaments thereof. Following the coolant water bath the implant unit such as 10 of FIGS. 1 and 2 is removed from the mandrel and allowed to dry at room temperature.

The process as above described with reference to a single-tube or straight tubular implant 10 is generally similar for the bifurcate or Y-form of FIGS. 3 to 6. For this divided or plural tube form a special conformant mandrel is provided, indicated as a whole at 35, shown separately on a smaller scale in FIG. 6, in disassembled or preparatory condition in FIG. 5 and in use in FIGS. 3 and 4.

It will be understood that bifurcate implants 20, FIGS. 3 and 4, are useful for replacement of vascular junctures, especially that of the large abdominal aorta and its division into the iliac limbs. Such Y-form implant 20 accordingly is formed with a stem or aortic portion 21 usually of relatively larger diameter and having at one end the iliac branches or legs 22, 22.

The plural-ply tubular fabric blank for this bifurcate form 20 is woven of the synthetic multi-filament warp and filling yarns in similar manner as already explained. Each of the woven tubular portions 21, 22, 22 is structurally similar to that of the single-tube implant of FIGS. 1 and 2 and as represented in detail in FIGS. 7 and 8 with the added feature of the branching and angling tubular structure. Thus in weaving the iliac legs 22 and the crotch or juncture thereof with the aortic stem 21, there is effected a calculated changing of the location of the cross-over lines of union S, S and S in the fillingwise direction for each pick or a small number of picks in each of the two plies. Under the patterned control of the shedding the legs 22, 22 are accorded the desired diameter and angular relation and the crotch area including the extreme point of the Y is integrally woven as a closed fabric structure of equal density with that at all other fabric areas, such that undesired leakage at the bifurcation point and adjacent region is obviated.

The bifurcate mandrel 35, FIGS. 3 to 5, is of similar composition and dimensioning relative to the implant blanks as described in connection with FIGS. 1 and 2. In this instance however it is so articulated that the stem section 36 and one or both leg sections 37, 37 are relatively detachable. While for some uses one leg 37 may be integral with the stem 36, it is found generally preferable that both legs be demountable as shown.

Separability is herein afforded as by provision of interconnecting plug and socket formations at the joints of the mating mandrel sections. In the illustrated example the stem 36 has at the end adjacent and containing the point of leg branching an appropriately flared and correspondingly flattened yoke 36a. Longitudinal sockets 38, 38 are let in from the transverse end wall of the yoke 36a, the sockets being relatively inclined at the angle desired for the mandrel legs 37. The socketed areas of the end wall of the yoke 36a are preferably disposed to be accurately perpendicular to the leg axes. At the proximate ends the mandrel legs 37, 37 are reduced to provide pins 5 39, 39 adapted for tight seating in the corresponding sockets 38, 38. The parts are accurately machined and finished so that the leg shoulders at the base of the pins tightly abut the end wall of the stem yoke 36a and the cylindrical outer walls of the legs flow substantially without interruption into the circumferential surface of the stem 36 and its yoke 36a. The flattening of the latter across the flared portion is made to compensate for the flare; that is, the circumference at the yoke 35a is kept at or not materially greater than for the main cylindrical portion of the stem 36 so that little or no distention of the tubular fabric blank occurs in the micro-crimping operation.

For vascular implant purposes the iliac legs of a Y-form implant generally are each smaller in diameter than that of the aortic stern but in the practice of the invention they may approach or substantially equal that of the aortic Tubular Bifurcations Aortic Iliac Flat Open Flat Open Diameter, Diameter, Diameter, Diameter, mm mm mm. mm.

22. 3 14.6 15.3 10. 0 29. 9 19.0 18. 3 12. 4 44. 6 28. 7 23. 1 15. 2 44.6 28. 7 39. 5 and 23. 4 27. 6 and 15.8 52. 2 33. 3 23. 1 15. 8 52. 2 33. 7 30. 3 19. 4 59. 8 38. 3 23. 4 15.0 59. 8 38. 2 3l. 0 20. 0 37. 6 24. 0 18. 7 1

The open diameter values in the above table are also the diameter of the corresponding mandrels at room temperature.

As in the case of the single-tube implants the Y-form mandrel diameters, for the aortic stem 36 and for the iliac legs 37, 37 are scaled to have at room temperature diameter sizes the same as the lumen or open diameter values such as above indicated. It is noted that implant item No. 4 of the above table has iliac limbs differing from each other in diameter; also that implant items Nos. 5 and 6 and also Nos. 7 and 8 show instances of a given same size of aortic stem available with different sizes of legs.

In any instance the bifurcate mandrels such as 35 are accurately scaled as to stem and leg diameter to that desired for the particular implant. And in any instance the mandrels 35 are so constructed, having reference to the leg diameters relative to the stem and to each other that the two legs are sufficiently spaced at the point of juncture with the mandrel stem so that the tubular fabric of the respective legs can be compressively installed fully to the end wall of the stem yoke 36a.

In the compressive installation of a Y-form implant blank 20A onto a mandrel 35 the procedure is generally similar as described with respect to the straight form blank of FIGS. 1 and 2. Where both mandrel legs are demountable the legs of the fabric blank may be brought onto them in either direction accordingly as the blank stem is installed before or after the blank legs. More conveniently the blank stem is first compressed onto the mandrel stem 36 at the yoke end 3611 of the latter and the mandrel legs 37, 37 then inserted through the blank legs, set into the stem sockets 38 and the compressive microcrimping completed for the entire blank. Obviously with one mandrel leg integral the fabric blank is installed by first passing the stem of the blank over the integral leg of the mandrel.

The operation of mounting the blank on the mandrel again is accomplished with attendant axial compression such that'the blank is reduced to the approximate 25% of the overall initial length. In the area of the crotch at the junction of the legs with the stem the microcrimping is substantially continuous, With the innermost pleats 15 of the leg members merging directly into the pleats 15a of the stem, with the fabric of the first stem pleat brought radially inward centrally between the legs into conformity with the end wall of the stem yoke 36a and affording crotch-closing fillets uniting all three tubular elements of the implant. Such fillet or crotchclosing wall portion is seen at 23, FIGS. 3 and 4. It has a general hour-glass shape corresponding to the central inter-socket area 36x of the mandrel yoke 36a, FIG. 5.

By way of additional precaution at the area of maximum vulnerability to leakage under abnormal conditions, the Y-form implants 20 after being thoroughly dried following the processing as described in connection With FIGS. 1 and 2 are coated at the crotch area with an aqueous solution of polyvinyl and allowed to air dry. Thereafter the coated area is cured as by placing the implant in an oven at about 250 F. for a period to average about five minutes.

The prosthetic implants and 20 as herein disclosed possess such flexibility and resilience that they are free of kinking, objectionable stricture or collapse not only under fiexure of the shorter lengths of cm. and cm. through a full 360 of bend but such length can be tied into a throw-knot or given a full twist between the ends and will still maintain an open lumen. They possess the further advantage among others that they can be supplied not only as units fashioned to exact surgical specifications but also in extra or indefinite lengths for cutting to proper lengths in the operating room. Likewise an implant of specified length may if required be extended axially for additional attaching length even in the course of operative implantation.

The resultant vascular implants of the invention are showing excellent results both in animal and in clinical work in which they have been used to replace segments of the aorta and/or peripheral arteries, or as shunts, thereby importantly contributing to progress in the field of cardiovascular surgery.

My invention is not limited to the particular embodiments thereof illustrated and described herein, and I set forth its scope in my following claims.

I claim:

1. A vascular prosthetic implant comprising a tubular fabric body circumferentially integrally fashioned of sterilizable tissue-compatible synthetic multi-filament yarns having a fineness of the order of denier and being compactly disposed in the fabric of the tubular body for according thereto a predetermined limited but tissue-growth-promoting porosity value in the range of about 16 to 30 in terms of cubic feet of air a minute per square foot of fabric at a pressure of 1.26 in. of water,

said tubular implant body having a normally open lumen Within a uniform-diametered cylindrical interior Wall defined by axially continguous and effectively continuous smooth fabric rings spanning between the inner bases of and held open by external circumferential micro-crimps of outward extent substantially less than the lumen radius and disposed in axially compacted randomly contiguous array for structurally affording to the implant in the absence of additive fabric stiffening treatment the capacity of self-maintenance in open lumen status under subjection to expectable use fiexure and of selfrestoration to such open status on release of tem porarily constricting external pressure,

said tubular implant in said normal open form possessing high lateral flexibility and resilience and being elastically extensible and contractible axially.

2. A vascular prosthetic implant according to claim 1 fashioned as a single continuous tube.

3. A vascular prosthetic implant according to claim 1 fashioned in bifurcate form including a tubular main stem and angular legs branching integrally from one end thereof, the stem and legs being similarly fashioned with said inner-wall rings and said outer-wall axially compacted micro-crimps in continuous array from end to end of the implant as a whole, and the juncture of the stem and legs being integral and merging into a central crotchclosing fillet of the constituent fabric.

References Cited in the file of this patent UNITED STATES PATENTS 2,127,903 Bowen Aug. 23, 1938 2,347,101 Harding Apr. 18, 1944 2,462,239 Van Dinter et al. Feb. 22, 1949 2,836,181 Tapp May 27, 1958 2,854,695 Moreau Oct. 7, 1958 2,924,250 Sidebotham Feb. 9, 1960 2,990,605 Demsyk July 4, 1961 3,019,820 Yowell et al. Feb. 6, 1962

Claims (1)

1. A VASCULAR PROSTHETIC IMPLANT COMPRISING A TUBULAR FABRIC BODY CIRCUMFERENTIALLY INTEGRALLY FASHIONED OF STERILIZABLE TISSUE-COMPATIBLE SYNTHETIC MULTI-FILAMENT YARNS HAVING A FINENESS OF THE ORDER OF 70 DENIER AND BEING COMPACTLY DISPOSED IN THE FABRIC OF THE TUBULAR BODY FOR ACCORDING THERETO A PREDETERMINED LIMITED BUT TISSUE-GROWTH-PROMOTING POROSITY VALUE IN THE RANGE OF ABOUT 16 TO 30 IN TERMS OF CUBIC FEET OF AIR A MINUTE PER SQUARE FOOT OF FABRIC AT A PRESSURE OF 1.26 IN. OF WATER, SAID TUBULAR IMPLANT BODY HAVING A NORMALLY OPEN LUMEN WITHIN A UNIFORM-DIAMETERED CYLINDRICAL INTERIOR WALL DEFINED BY AXIALLY CONTINGUOUS AND EFFECTIVELY CONTINUOUS SMOOTH FABRIC RINGS SPANNING BETWEEN THE INNER BASES OF AND HELD OPEN BY EXTERNAL CIRCUMFERENTIAL MICRO-CRIMPS OF OUTWARD EXTENT SUBSTANTIALLY LESS THAN THE LUMEN RADIUS AND DISPOSED IN AXIALLY COMPACTED RANDOMLY CONTIGUOUS ARRAY FOR STRUCTURALLY AFFORDING TO THE IMPLANT IN THE ABSENCE OF ADDITIVE FABRIC STIFFENING TREATMENT THE CAPACITY OF SELF-MAINTENANCE IN OPEN LUMEN STATUS UNDER SUBJECTION TO EXPECTABLE USE FLEXURE AND OF SELFRESTORATION TO SUCH OPEN STATUS ON RELEASE OF TEMPORARILY CONSTRICTING EXTERNAL PRESSURE, SAID TUBULAR IMPLANT IN SAID NORMAL OPEN FORM POSSESSING HIGH LATERAL FLEXIBILITY AND RESILIENCE AND BEING ELASTICALLY EXTENSIBLE AND CONTRACTIBLE AXIALLY.
US3142067A 1958-11-21 1961-02-16 Synthetic vascular implants Expired - Lifetime US3142067A (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
US3096560A US3096560A (en) 1958-11-21 1958-11-21 Process for synthetic vascular implants
US3142067A US3142067A (en) 1958-11-21 1961-02-16 Synthetic vascular implants

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US3142067A US3142067A (en) 1958-11-21 1961-02-16 Synthetic vascular implants

Publications (1)

Publication Number Publication Date
US3142067A true US3142067A (en) 1964-07-28

Family

ID=26781012

Family Applications (1)

Application Number Title Priority Date Filing Date
US3142067A Expired - Lifetime US3142067A (en) 1958-11-21 1961-02-16 Synthetic vascular implants

Country Status (1)

Country Link
US (1) US3142067A (en)

Cited By (41)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0004667A1 (en) * 1978-04-07 1979-10-17 Precimed S.A. Cardiac probe
US4502159A (en) * 1982-08-12 1985-03-05 Shiley Incorporated Tubular prostheses prepared from pericardial tissue
US4652263A (en) * 1985-06-20 1987-03-24 Atrium Medical Corporation Elasticization of microporous woven tubes
US4892539A (en) * 1988-02-08 1990-01-09 D-R Medical Systems, Inc. Vascular graft
US4915893A (en) * 1982-07-16 1990-04-10 Medtronic, Inc. Method of preparing polyester filament material
US5110852A (en) * 1982-07-16 1992-05-05 Rijksuniversiteit Te Groningen Filament material polylactide mixtures
US5489295A (en) * 1991-04-11 1996-02-06 Endovascular Technologies, Inc. Endovascular graft having bifurcation and apparatus and method for deploying the same
WO1998027893A2 (en) 1996-12-23 1998-07-02 Prograft Medical, Inc. Kink resistant bifurcated prosthesis
WO1998027895A1 (en) 1996-12-23 1998-07-02 Prograft Medical, Inc. Endolumenal stent-graft with leak-resistant seal
US6117117A (en) * 1998-08-24 2000-09-12 Advanced Cardiovascular Systems, Inc. Bifurcated catheter assembly
US6165195A (en) * 1997-08-13 2000-12-26 Advanced Cardiovascylar Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6221090B1 (en) 1997-08-13 2001-04-24 Advanced Cardiovascular Systems, Inc. Stent delivery assembly
US6254593B1 (en) 1999-12-10 2001-07-03 Advanced Cardiovascular Systems, Inc. Bifurcated stent delivery system having retractable sheath
US6331188B1 (en) 1994-08-31 2001-12-18 Gore Enterprise Holdings, Inc. Exterior supported self-expanding stent-graft
US6352561B1 (en) 1996-12-23 2002-03-05 W. L. Gore & Associates Implant deployment apparatus
US6352553B1 (en) 1995-12-14 2002-03-05 Gore Enterprise Holdings, Inc. Stent-graft deployment apparatus and method
US6361637B2 (en) 1995-12-14 2002-03-26 Gore Enterprise Holdings, Inc. Method of making a kink resistant stent-graft
US6361544B1 (en) 1997-08-13 2002-03-26 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6361555B1 (en) 1999-12-15 2002-03-26 Advanced Cardiovascular Systems, Inc. Stent and stent delivery assembly and method of use
US6383213B2 (en) 1999-10-05 2002-05-07 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6387120B2 (en) 1999-12-09 2002-05-14 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US20020058984A1 (en) * 1998-03-30 2002-05-16 Frank Butaric Extension prosthesis for an arterial repair
US6544219B2 (en) 2000-12-15 2003-04-08 Advanced Cardiovascular Systems, Inc. Catheter for placement of therapeutic devices at the ostium of a bifurcation of a body lumen
WO2003049644A1 (en) 2001-12-07 2003-06-19 Boston Scientific Limited Anatomically curved graft for implantation at the aortic arch
US6582394B1 (en) 2000-11-14 2003-06-24 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcated vessels
US6613072B2 (en) 1994-09-08 2003-09-02 Gore Enterprise Holdings, Inc. Procedures for introducing stents and stent-grafts
US6626938B1 (en) * 2000-11-16 2003-09-30 Cordis Corporation Stent graft having a pleated graft member
US6673107B1 (en) 1999-12-06 2004-01-06 Advanced Cardiovascular Systems, Inc. Bifurcated stent and method of making
US6709440B2 (en) 2001-05-17 2004-03-23 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US20050256567A1 (en) * 2004-05-14 2005-11-17 St. Jude Medical, Inc. Heart valve annuloplasty prosthesis sewing cuffs and methods of making same
US20050283224A1 (en) * 2004-06-22 2005-12-22 Scimed Life Systems, Inc. Implantable medical devices with antimicrobial and biodegradable matrices
US7090694B1 (en) 2003-11-19 2006-08-15 Advanced Cardiovascular Systems, Inc. Portal design for stent for treating bifurcated vessels
US20060264138A1 (en) * 2001-06-11 2006-11-23 Scimed Life Systems, Inc. Composite ePTFE/textile prosthesis
US7314483B2 (en) 2000-11-16 2008-01-01 Cordis Corp. Stent graft with branch leg
US20080009829A1 (en) * 2006-07-07 2008-01-10 Abbott Cardiovascular Systems Inc. Balloon catheter having a branched distal section with secured branches
US20080051876A1 (en) * 2006-08-22 2008-02-28 Advanced Cardiovascular Systems, Inc. Intravascular stent
US20080086190A1 (en) * 2006-08-22 2008-04-10 Diem Uyen Ta Intravascular stent
USRE40404E1 (en) 1994-08-02 2008-06-24 Maquet Cardiovascular, Llp Thinly woven flexible graft
US20090012601A1 (en) * 2007-07-05 2009-01-08 Abbott Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US7753950B2 (en) 1997-08-13 2010-07-13 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US20120012569A1 (en) * 2010-07-14 2012-01-19 Danny Severino Fabric cutting system and method

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2127903A (en) * 1936-05-05 1938-08-23 Davis & Geck Inc Tube for surgical purposes and method of preparing and using the same
US2347101A (en) * 1941-05-20 1944-04-18 Us Rubber Co Method of making corrugated tubes
US2462239A (en) * 1944-08-23 1949-02-22 Mishawaka Rubber & Woolen Mfg Boot form
US2836181A (en) * 1955-01-17 1958-05-27 Chemstrand Corp Flexible nylon tube and method for preparing same
US2854695A (en) * 1956-06-13 1958-10-07 Davol Rubber Co Catheter molding form
US2924250A (en) * 1957-11-26 1960-02-09 John B Sidebotham Bifurcated textile tubes and method of weaving the same
US2990605A (en) * 1957-01-30 1961-07-04 Demsyk Paul Method of forming artificial vascular members
US3019820A (en) * 1957-02-28 1962-02-06 Joseph W Yowell Corrugated tubing

Patent Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2127903A (en) * 1936-05-05 1938-08-23 Davis & Geck Inc Tube for surgical purposes and method of preparing and using the same
US2347101A (en) * 1941-05-20 1944-04-18 Us Rubber Co Method of making corrugated tubes
US2462239A (en) * 1944-08-23 1949-02-22 Mishawaka Rubber & Woolen Mfg Boot form
US2836181A (en) * 1955-01-17 1958-05-27 Chemstrand Corp Flexible nylon tube and method for preparing same
US2854695A (en) * 1956-06-13 1958-10-07 Davol Rubber Co Catheter molding form
US2990605A (en) * 1957-01-30 1961-07-04 Demsyk Paul Method of forming artificial vascular members
US3019820A (en) * 1957-02-28 1962-02-06 Joseph W Yowell Corrugated tubing
US2924250A (en) * 1957-11-26 1960-02-09 John B Sidebotham Bifurcated textile tubes and method of weaving the same

Cited By (93)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0004667A1 (en) * 1978-04-07 1979-10-17 Precimed S.A. Cardiac probe
US4915893A (en) * 1982-07-16 1990-04-10 Medtronic, Inc. Method of preparing polyester filament material
US5110852A (en) * 1982-07-16 1992-05-05 Rijksuniversiteit Te Groningen Filament material polylactide mixtures
US4502159A (en) * 1982-08-12 1985-03-05 Shiley Incorporated Tubular prostheses prepared from pericardial tissue
US4652263A (en) * 1985-06-20 1987-03-24 Atrium Medical Corporation Elasticization of microporous woven tubes
US4892539A (en) * 1988-02-08 1990-01-09 D-R Medical Systems, Inc. Vascular graft
US5489295A (en) * 1991-04-11 1996-02-06 Endovascular Technologies, Inc. Endovascular graft having bifurcation and apparatus and method for deploying the same
US6210435B1 (en) 1991-04-11 2001-04-03 Endovascular Technologies, Inc. Endovascular graft having bifurcation and apparatus and method for deploying the same
US6214038B1 (en) 1991-04-11 2001-04-10 Endovascular Technologies, Inc. Method for deploying an endovascular graft having a bifurcation
US5824039A (en) * 1991-04-11 1998-10-20 Endovascular Technologies, Inc. Endovascular graft having bifurcation and apparatus and method for deploying the same
USRE40404E1 (en) 1994-08-02 2008-06-24 Maquet Cardiovascular, Llp Thinly woven flexible graft
US6517570B1 (en) 1994-08-31 2003-02-11 Gore Enterprise Holdings, Inc. Exterior supported self-expanding stent-graft
US8623065B2 (en) 1994-08-31 2014-01-07 W. L. Gore & Associates, Inc. Exterior supported self-expanding stent-graft
US6331188B1 (en) 1994-08-31 2001-12-18 Gore Enterprise Holdings, Inc. Exterior supported self-expanding stent-graft
US6613072B2 (en) 1994-09-08 2003-09-02 Gore Enterprise Holdings, Inc. Procedures for introducing stents and stent-grafts
US6352553B1 (en) 1995-12-14 2002-03-05 Gore Enterprise Holdings, Inc. Stent-graft deployment apparatus and method
US6361637B2 (en) 1995-12-14 2002-03-26 Gore Enterprise Holdings, Inc. Method of making a kink resistant stent-graft
US6520986B2 (en) 1995-12-14 2003-02-18 Gore Enterprise Holdings, Inc. Kink resistant stent-graft
US8323328B2 (en) 1995-12-14 2012-12-04 W. L. Gore & Associates, Inc. Kink resistant stent-graft
US6015431A (en) * 1996-12-23 2000-01-18 Prograft Medical, Inc. Endolumenal stent-graft with leak-resistant seal
WO1998027893A2 (en) 1996-12-23 1998-07-02 Prograft Medical, Inc. Kink resistant bifurcated prosthesis
US6352561B1 (en) 1996-12-23 2002-03-05 W. L. Gore & Associates Implant deployment apparatus
US7682380B2 (en) 1996-12-23 2010-03-23 Gore Enterprise Holdings, Inc. Kink-resistant bifurcated prosthesis
US20090138066A1 (en) * 1996-12-23 2009-05-28 Leopold Eric W Implant Deployment Apparatus
WO1998027895A1 (en) 1996-12-23 1998-07-02 Prograft Medical, Inc. Endolumenal stent-graft with leak-resistant seal
US20020165603A1 (en) * 1996-12-23 2002-11-07 Troy Thornton Kink-resistant bifurcated prosthesis
US6165195A (en) * 1997-08-13 2000-12-26 Advanced Cardiovascylar Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6955688B2 (en) 1997-08-13 2005-10-18 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US7753950B2 (en) 1997-08-13 2010-07-13 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US7955379B2 (en) 1997-08-13 2011-06-07 Abbott Cardiovascular Systems Inc. Stent and catheter assembly and method for treating bifurcations
US6428567B2 (en) 1997-08-13 2002-08-06 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6896699B2 (en) 1997-08-13 2005-05-24 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6579312B2 (en) 1997-08-13 2003-06-17 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6264682B1 (en) 1997-08-13 2001-07-24 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6221098B1 (en) 1997-08-13 2001-04-24 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6508836B2 (en) 1997-08-13 2003-01-21 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6221090B1 (en) 1997-08-13 2001-04-24 Advanced Cardiovascular Systems, Inc. Stent delivery assembly
US6361544B1 (en) 1997-08-13 2002-03-26 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6875229B2 (en) 1997-08-13 2005-04-05 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6887268B2 (en) 1998-03-30 2005-05-03 Cordis Corporation Extension prosthesis for an arterial repair
US20020058984A1 (en) * 1998-03-30 2002-05-16 Frank Butaric Extension prosthesis for an arterial repair
US6475208B2 (en) 1998-08-24 2002-11-05 Advanced Cardiovascular Systems, Inc. Bifurcated catheter assembly
US6117117A (en) * 1998-08-24 2000-09-12 Advanced Cardiovascular Systems, Inc. Bifurcated catheter assembly
US6210380B1 (en) 1998-08-24 2001-04-03 Advanced Cardiovascular Systems, Inc. Bifurcated catheter assembly
US20030093109A1 (en) * 1998-08-24 2003-05-15 Mauch Kevin M. Bifurcated catheter assembly
US6780174B2 (en) 1998-08-24 2004-08-24 Advanced Cardiovascular Systems, Inc. Bifurcated catheter assembly
US6494875B1 (en) 1998-08-24 2002-12-17 Advanced Cardiovascular Systems, Inc. Bifurcated catheter assembly
US6383213B2 (en) 1999-10-05 2002-05-07 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6673107B1 (en) 1999-12-06 2004-01-06 Advanced Cardiovascular Systems, Inc. Bifurcated stent and method of making
US6387120B2 (en) 1999-12-09 2002-05-14 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6371978B1 (en) 1999-12-10 2002-04-16 Advanced Cardiovascular Systems, Inc. Bifurcated stent delivery system having retractable sheath
US6802856B2 (en) 1999-12-10 2004-10-12 Advanced Cardiovascular Systems, Inc. Bifurcated stent delivery system having retractable sheath
US20050043779A1 (en) * 1999-12-10 2005-02-24 Wilson W. Stan Bifurcated stent delivery system having retractable sheath
US20020111675A1 (en) * 1999-12-10 2002-08-15 Wilson W. Stan Bifurcated stent delivery system having retractable sheath
US6254593B1 (en) 1999-12-10 2001-07-03 Advanced Cardiovascular Systems, Inc. Bifurcated stent delivery system having retractable sheath
US7481837B2 (en) 1999-12-10 2009-01-27 Advanced Cardiovascular Systems, Inc. Bifurcated stent delivery system having retractable sheath
US6599315B2 (en) 1999-12-15 2003-07-29 Advanced Cardiovascular Systems, Inc. Stent and stent delivery assembly and method of use
US6361555B1 (en) 1999-12-15 2002-03-26 Advanced Cardiovascular Systems, Inc. Stent and stent delivery assembly and method of use
US6582394B1 (en) 2000-11-14 2003-06-24 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcated vessels
US7862609B2 (en) 2000-11-16 2011-01-04 Cordis Corporation Stent graft having a pleated graft member
US6626938B1 (en) * 2000-11-16 2003-09-30 Cordis Corporation Stent graft having a pleated graft member
US7314483B2 (en) 2000-11-16 2008-01-01 Cordis Corp. Stent graft with branch leg
US6544219B2 (en) 2000-12-15 2003-04-08 Advanced Cardiovascular Systems, Inc. Catheter for placement of therapeutic devices at the ostium of a bifurcation of a body lumen
US6709440B2 (en) 2001-05-17 2004-03-23 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6749628B1 (en) 2001-05-17 2004-06-15 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US20060264138A1 (en) * 2001-06-11 2006-11-23 Scimed Life Systems, Inc. Composite ePTFE/textile prosthesis
EP1399200B2 (en) 2001-06-11 2014-07-02 Boston Scientific Limited COMPOSITE ePTFE/TEXTILE PROSTHESIS
WO2003049644A1 (en) 2001-12-07 2003-06-19 Boston Scientific Limited Anatomically curved graft for implantation at the aortic arch
US7465315B2 (en) 2003-11-19 2008-12-16 Advanced Cardiovascular Systems, Inc. Portal design for stent for treating bifurcated vessels
US7090694B1 (en) 2003-11-19 2006-08-15 Advanced Cardiovascular Systems, Inc. Portal design for stent for treating bifurcated vessels
US20060265050A1 (en) * 2003-11-19 2006-11-23 Grayson Morris Portal design for stent for treating bifurcated vessels
US7938856B2 (en) * 2004-05-14 2011-05-10 St. Jude Medical, Inc. Heart valve annuloplasty prosthesis sewing cuffs and methods of making same
US20110238170A1 (en) * 2004-05-14 2011-09-29 St. Jude Medical, Inc. Heart valve annuloplasty prosthesis sewing cuffs and methods of making same
US9289294B2 (en) 2004-05-14 2016-03-22 St. Jude Medical, Inc. Heart valve annuloplasty prosthesis sewing cuffs and methods of making same
US20050256567A1 (en) * 2004-05-14 2005-11-17 St. Jude Medical, Inc. Heart valve annuloplasty prosthesis sewing cuffs and methods of making same
US7794490B2 (en) 2004-06-22 2010-09-14 Boston Scientific Scimed, Inc. Implantable medical devices with antimicrobial and biodegradable matrices
US20100324667A1 (en) * 2004-06-22 2010-12-23 Boston Scientific Scimed, Inc. Implantable medical devices with anti-microbial and biodegradable matrices
US8192481B2 (en) 2004-06-22 2012-06-05 Boston Scientific Scimed, Inc. Implantable medical devices with anti-microbial and biodegradable matrices
US20050283224A1 (en) * 2004-06-22 2005-12-22 Scimed Life Systems, Inc. Implantable medical devices with antimicrobial and biodegradable matrices
US20080009829A1 (en) * 2006-07-07 2008-01-10 Abbott Cardiovascular Systems Inc. Balloon catheter having a branched distal section with secured branches
US20080009933A1 (en) * 2006-07-07 2008-01-10 Diem Uyen Ta Catheter assembly and method for treating bifurcations
US8029558B2 (en) 2006-07-07 2011-10-04 Abbott Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US20080009932A1 (en) * 2006-07-07 2008-01-10 Diem Uyen Ta Stent and catheter assembly and method for treating bifurcations
US7959667B2 (en) 2006-07-07 2011-06-14 Abbott Cardiovascular Systems Inc. Catheter assembly and method for treating bifurcations
US8882826B2 (en) 2006-08-22 2014-11-11 Abbott Cardiovascular Systems Inc. Intravascular stent
US20080051876A1 (en) * 2006-08-22 2008-02-28 Advanced Cardiovascular Systems, Inc. Intravascular stent
US20080086190A1 (en) * 2006-08-22 2008-04-10 Diem Uyen Ta Intravascular stent
US8834554B2 (en) 2006-08-22 2014-09-16 Abbott Cardiovascular Systems Inc. Intravascular stent
US20090012601A1 (en) * 2007-07-05 2009-01-08 Abbott Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US8540619B2 (en) * 2010-07-14 2013-09-24 Atex Technologies, Inc. Fabric cutting system and method
US20120012569A1 (en) * 2010-07-14 2012-01-19 Danny Severino Fabric cutting system and method
US9038514B2 (en) * 2010-07-14 2015-05-26 Atex Technologies, Inc. Fabric cutting system and method
US20130338432A1 (en) * 2010-07-14 2013-12-19 Atex Technologies, Inc. Fabric Cutting System and Method

Similar Documents

Publication Publication Date Title
US3479670A (en) Tubular prosthetic implant having helical thermoplastic wrapping therearound
US3588920A (en) Surgical vascular prostheses formed of polyester fiber paper
US3526906A (en) Prosthetic implants made from carbonaceous materials
US5674277A (en) Stent for placement in a body tube
US6174328B1 (en) Intraluminal stent and graft
US6860900B2 (en) Stent and stent-graft for treating branched vessels
US5972441A (en) Thin-wall polytetrafluoroethylene tube
US5385580A (en) Self-supporting woven vascular graft
US6245099B1 (en) Selective adherence of stent-graft coverings, mandrel and method of making stent-graft device
US5824040A (en) Endoluminal prostheses and therapies for highly variable body lumens
US6221102B1 (en) Intraluminal grafting system
US6019791A (en) Buttress for cardiac valve reconstruction
US6464721B1 (en) Bifurcated graft with a superior extension
US6042605A (en) Kink resistant stent-graft
US6187033B1 (en) Aortic arch prosthetic graft
US6025044A (en) Thin-wall polytetrafluoroethylene tube
US6280466B1 (en) Endovascular graft system
EP0480667B1 (en) Percutaneous stent assembly
US2836181A (en) Flexible nylon tube and method for preparing same
US6547814B2 (en) Selective adherence of stent-graft coverings
US4517687A (en) Synthetic woven double-velour graft
US5697970A (en) Thinly woven flexible graft
US6911040B2 (en) Covered segmented stent
US6068656A (en) Coronary stent
US6814754B2 (en) Woven tubular graft with regions of varying flexibility