CA2122716A1 - Silicone/dracon composite vascular graft - Google Patents

Abstract

A silicone/DACRON (16, 18) composite vascular graft (10) especially well suited as an arteriovenous (A-V) graft fistula for dialysis application. Distinct uniquenesses include the ability to seal around needle puncture holes without externally applied pressure, excellent anti-kink, anti-crush and strength properties, and a smooth non-porous inner surface which reduces thrombus deposition and enhances the graft wall compliance or elasticity.

Description

WO 93/08768 PCr/US92/09359 ~1~2716 8ILICONE~D~CRON COMPO8ITE: 'VA~CULAR G}~AFT
CRO8~ ~EFERE:NCE8 TO C~--~ENDING APPLICATIOM~3 None.
B~CRGRO~ND OF T~ Nq!ION
1. Fiel~ of the Invention - The present invention pertains to a silicone/DAC~ON0 composite vascular graft, especially well suited as an arteriovenous (A-V) graft fistula for patients requiring long-term vascular access, such as in the case of chronic kidney dialysis.

2. Dascription of_the Prior Art - Other silicone grafts have been developed in the past using a variety of construction methods. The benefits of silicone material were described in U.S. Patent 4,687,482. A DACRON outer support, which prevents aneurysm is described in U.S.
Patent Nos. 4,657,544 and 4,629,458. White and Roy have patents which use silicone impregnated into sea urchin skeleton to form a porous structure once the skeleton is - ..
dissolved away in U.S. Patent Nos. 3,890,107 and 3:,929,~71~
: `
An electrostatic spinning technology has been patented for use in primarily polyurethane grafts in U.S.
,~ i Patent Nos. 4,043,331; 4,044,404; 4,639rl86; 4,127,706;
; 4,345,~14; 4,323,525; and 4,878,908. These patents were ~: used to spin polyurethane fibers. Without the addition of Infra Red (IR) curing as part of the immediate fiber .

W093~08768 PCT/US92/093~9 21~271g .

curing process, the silicone fibers would meld together and form a clump.
~UMMARY OF ~HE INVEN~ION
The general purpose of the present invention is to provide a silicone/DACRON composite vascular graft for use as an artificial blood vessel, espe~ially an arteriovenous (A-V) graft fistula providing long-term vascular access for kidney dialysis applications.
According to one embodiment of the present invention, there is provided a graft including a non-porous, smooth inner blood contact surface which reduces thrombus deposition; a silicone bead spiral or ring for anti-kink and anti-crush; a DACRON wind primarily for added strength; a small pore bulk construction with an impermeable inner surface which reduces fibroblast ingrowth and helps maintain compliance; continued elasticity allows excellent needle puncture sealing immediately and over time without applying external pressure; and the DACRON wind is coated with silicone to prevent body tissue from contacting DACRON which is a very thrombogenic material.
According to the process for the embodiment of the _ . .
present inYention, the use of IR energy partially cures the silicone strand before it contacts the mandrel; the order of construction of the graft enhances the strength, anti-crush, and anti-kink; the angle of applying the '. .

W O 93/08768 PC~r/US92/09359 DACRON yarn and placement on top of the silicone bead allows the DACRON filaments to move relative to its repeat unit neighbor to help reduce any tendency toward graft kinking; and the silicone is dispersed in solvent for electrostatic spinning.
In another embodiment of the present invention, the blood contacting surface of the graft can be of a fibrous porous construction, similar but not necessarily identical, in structure to the middle and outer porous structure of the first embodiment. The pore size may range from approximately 2 microns to loO microns. The porous inner surface will allow cellular attachment to ~the inside surface of the graft. These cells may '~
originate from cells located at the junction of the graft with the native vessel, from cells that grow through the walls of the graft~fro the outside tissue or from the blood itself. The porous inner surface may enhance long term patency of the graft in vascular graf'_ing situations where~the blood~flow rate is relatively low.
In yet another embodiment of the present invention, the graft can be constructed without the DACRON yarn filam,ent. The function of the graft will be suitable for mo-t vascular graft applications; the strength of the graft to resist aneurysm or suture pullout will be somewhat reduced.

::: ~ :

W O 93/08768 2 1 2 2 7 1 6 PC~r/US92/09359 The significant aspects, advantages and uniqueness -~
of this graft in summary are: 1) the non-porous smooth ~-silicone blood contact surface, which reduces thrombus deposit; 2) the bulk pore size and the solid inner surface, results in needle puncture sealing immediately and over time without applying external pressure; 3) the use of IR energy along with electrostatic spinning; 4) the application of a siliconé bead for anti-kink and :
anti-crush; S) the application of DACRON yarn for strength without any significant reduction in anti-kink ~-properties of the graft; 6) the coating of the DACRON
yarn with silicone prior to its application onto the graft; and 7) the bulk pore size and solid inner surface which tends to allow reticulocyte penetration into the .:~:
porous portion of the graft, but not much fibroblastic ingrowth, results in retaini~ng graft compliance or elasticity over time.
Another significant aspect and feature of the process is construction which uses electrostatic spinning or spraying technology to form a fibrous and porous silicone structure that is found in much of the graft wall. This electrostatic technology is also used to apply the non-porous smooth silicone layer directly onto a mandrel and form the blood contact surface after removal of the graft from the mandrel.

~ .

WO 93/08768 PCl /US92/09359 BRIEF DE8C3?IPTION OF q~ D~WIN~8 Other objects of the present invention and many of the attendant advant~ges of the present invention will be readily appreciated as the same becomes better understood by reference to the following detailed description when considered in connection with the accompanying drawings, in which like reference numerals designate like parts throughout the figures thereof and wherein:
~ IG~ 1 illustrates a plan view of a vascular graft;
~ IG. 2 illustrates a partial cross-sectional view of FIG. l;
FI~. 3 illustrates a first alternative embodiment;
and, FIG. ~ illustrates a second alternative embodiment.
DE~CRIPTION OF T~E PREF~RRED ENBODIM~N~
FIG. 1 i}lustrates a plan view of the graft 10.
F~G. 2 illustrates a partial cross-sectional view of FIG. 1. A meld layer 12 is first applied to a mandre spinning at low rpm (approximately 200 rpm) with IR
heater off, but with the electrostatic spinning voltages of the grid and m`andrel activated. This allows a uniform layer of silicone to be deposited onto the mandrel formihg a blood contact surface that is as smooth as the mandrel finish and impermeable to blood, plasma, or cellular penetration. The high flow rate of blood which vill move through the ~raft 10 will holp prevent thro~bus W093/08768 PCT/US~2/09359 deposition on the smooth surface. Since blood or plasma cannot penetrate this layer, this graft 10 does not require preclotting (a met~od required for some porous grafts whereby blood is allowed to clot within the graft wall to prevent seepage or bleeding through the graft walls). This non-porous inner meld layer 12 also reduces the amount of fibroblastic cell penetration into the graft 10 from the outside surface. Fibroblastic ingrowth generally results in the deposition of collagen within the pores of porous grafts and significantly reduces the flexibility of the graft lO over time. The reduction in fibroblastic ingrowth into the walls of this graft 10 alIows it to remain flexible and thereby maintain its needle puncture hole sealing characteristic, as well as its flexibility and anti-kink properties.
The next layer, which is applied on top of the non-porous meld layer 12, is the porous silicone middle layer 14. To form individual fi~ers the mandrel is spun at a much faster rate (approximately 4000 rpm). The I~ heater and the electrostatic voltages are both activated. The fibers are partially cured before they contact the mandrel due to the application of IR energy. The porosity of this layer can be controlled by adjusting the amount of fiber cure prior to deposition onto the mandrel. This layer provides fibrous structure of the graft 10 which serves as a framework to hold the silicone W O 93/08768 P{~r/US92~09359 212~716 bead 16 and DACRON yarn 18 that is applied on top of it, and to allow a structure that can expand and compress, and thereby contribute to the anti-kink character of the graft lo. This layer also contributes to graft strength and needle puncture sealing. The pore spacing and silicone fiber diameter range from 2 to 100 microns with a generally random occurrence. The pore size is of appropriate size to allow reticulocyte penetration into the graft wall, but not so large as to allow entry access to significant fibroblast penetration. Reticulocytes are - -cells which can panetrate into the small pore spaces, but generally do not depo~it significant collagenous material that can result in loss of graft elasticity and needle hole sealing characteristics.
A silicone bead 16 is then applied in a noncured form in a spiral configuration onto the porous middle layer 14 of the graft 10. This step is not done using electrostatics and involves simply extruding a silicone bead 16 onto a rotating graft 10 while moving transversely to form a spiral; the silicon~ bead 16 is then partially cured afterward. This spiral silicone beadl 16 serves to enhance the graft 10 anti-kinX and anti-crush properties by providing a structure which tends to maintain a circular cross section in the graft under compressive forces and forces which are generated `~
when the graft 10 is bent to a radius of curvature of 1 .

W093/08768 PC~/US~2/09359 2122~ 1 6 cm or less. ~his spiral silicone bead 16 could be replaced with a series of torus shaped rings spaced approximately as far apart as each repeat unit of the spiral. ;-On top of the silicone bead, a polyethylene terethalate (PET) or DACRON winding 18 is applied forming a series of spirals which are wound with both right handedness and left handedness winding directions. The presence of the DACRON winding 18 provides strength to the graft 10 so that the graft 10 does not exhibit weakness axially or radially with resultant aneurysm formation. The DACRON fibers also contribute to enhance -the pullout strength for sutures at the ends of the graft where they are sewn to native vessels. The positioning of the DACRON winding 18 over the silicone bead 16 allows the graft 10 to maintain excellent anti~
kink characteristics. Each DACRON strand can change its relative position to its neighboring repeat strand while the graft 10 is being bent, and thereby not inhibit bending. In addition, the presence of the DACRON strands in the graft wall tend to resist the formation of an oval cross section of the graft 10, and thereby contribute to enhanced anti-Xink and anti-crush characteristics for the graft 10. The DACRON could be replaced by other biostable filamentous materials. Currently, the DACRON
yarn is coated with silicone prior to its application W093/08768 PCT/USg~/09359 7 l ~

onto the graft 10 to insure that DACRON material is not put into direct contact with body tissue and to enhance DACRON to graft bonding..
The outer silicone layer 20 is applied using ELS
spinning and IR energy. It provides a porous outer layer that allows tissue to ingrow and anchor it in place in the subcutaneous tissue of the patient. It also helps to hold the DACRON winding 18 and silicone bead 16 in place.
The pore structure is similar to the middle porous layer and retains its elasticity due to minimal fibroblastic ingrowth.
D~8CRIPTION OF THB ALT~N~T~V~ ~$BODIM2NT~
The graft can be constructed in a manner identical with that of the preferred embodiment, however with an additional porous silicone inner layer that is first applied onto the mandrel. This inner layer 22 will allow tissue to attach to the gra-ft inner surface. A meld `
layer would then be applisd second and would serve to prevent blood or pla~ma penetration through the graft wall.
In yet ~nother embocliment, the graft is constructed in a manner identical to that of the pre~erred embodiment with the omission of the inner meld layer 12. With this construction, the inner surface consists of porous silicone fibers to allow good tissue attachment on the inner surface. In this case, the meld layer is not C~1~2716 ', ~.

present and tissue can penetrate through the entire wall of the graft from the outside of the graft to the inner surface.
In yet another embodiment, the graft can be constructed of another biostable polymeric material, other than silicone, that can be spun electros~atically. ~- ;
In yet another embodiment, the PET filament can be replaced by another biostable filament to provide additional graft strength.
In yet another embodiment, the silicone bead can be replaced by another biostable polymeric material that can - `
be bound to silicone, and provide the anti-Xink characteristics of the graft.
Various modifications can be made to the present invention without departing from the apparent scope hereof. There can be a coating or layer of the porous silicone middle layer material between the silicone bead and the polyethylene terethalate winding, although this is optional.
~ E C~IM:

~,

Claims (6)

1. A composite graft comprising in order:
a. a non-porous meld inner layer of silicone;
b. a porous silicone middle layer;
c. a silicone bead;
d. a polyethylene terethalate winding; and, e. a porous silicone outer layer.

2. A composite graft comprising in order:
a. a porous silicone inner layer;
b. a porous silicone middle layer which may vary in pore size from the inner layer;
c. a silicone bead;
d. a PET winding; and, e. a porous silicone outer layer.

3. Composite graft comprising in order:
a. a porous silicone inner layer;
b. a non-porous meld layer;
c. a porous silicone middle layer;
d. a silicone bead;
e. a PET winding; and, f. a porous silicone outer layer.

4. Composite graft comprising in order:
a. a non-porous smooth polymeric meld layer;
b. a porous polymeric middle layer;
c. a polymeric bead;
d. a polymeric winding; and, e. a porous polymeric outer layer.

5. A method of constructing a composite graft comprising in order:
a. spraying a non-porous meld inner layer of silicone unto a rotating mandrel;
b. electrostatically spinning silicone fibers, which have been partially cured using infrared energy onto rotating mandrel with partial graft;
c. extruding a silicone bead onto a rotating mandrel with partial graft while moving transversely;
d. winding a silicone coated non-static biocompatible thread in both right handedness and left handedness directions onto rotating mandrel with partial graft;
e. electrostatically spinning silicone fibers, which have been partially cured using infrared energy onto rotating mandrel with partial graft; and, f. dispersing the silicone in a suitable solvent for electrostatic spinning.

6. A method of controlling the porosity or percent void fraction in a porous silicone structure by controlling the amount of partial cure of the fibers and amount of melding of fiber prior to their deposition onto the mandrel.