Abstract:
An implantable intralumina device includes a multilayer composite tubular device supporting one or more stents between the layer thereof. A first porous elongate tube includes an exterior surface and an interior luminal surface. A radially expandable member is disposed about the exterior surface of the first tube. A second porous elongate tube is disposed concentrically over the first tube and is secured thereto so that the radially expandable member is longitudinally immobilized therebetween.

Description:
FIELD OF INVENTION  
         [0001]    The present invention relates generally to tubular implantable prosthetic devices such as vascular grafts and other endoprostheses. More particularly, the present invention relates to a graft formed of porous expanded polytetrafluoroethylene (ePTFE) which supports a stent in an ePTFE composite graft-stent device.  
         BACKGROUND OF THE INVENTION  
         [0002]    Intraluminal devices such as grafts and stents are known for treating stenosis, stricture, aneurysms and the like. These devices may be implanted either transluminally in a minimally invasive procedure or may be surgically implanted.  
           [0003]    Such intraluminal devices provide a technique for expanding a constricted vessel or for maintaining an open passageway through a vessel. One common technique used to hold open a blocked or constricted vessel such as a blood vessel is to employ a vascular stent. Stents are implantable intraluminal devices typically formed of wire which may be radially expanded to hold open constricted vessels. Thus, wire stents are useful to prevent restenosis of a dilated vessel or to eliminate the danger of reocclusion of the vessel. In addition, wire stents can also be used to reinforce various lumen in danger of collapse. However, stents are not generally designed as conduits or bypass devices.  
           [0004]    Intraluminal or endoprosthetic grafts, however, are designed as bypass devices which allow fluid flow therethrough. Often, these devices are percutaneously implanted within the vascular system to reinforce collapsing, partially occluded, weakened or abnormally dilated localized sections of, e.g., a blood vessel. Grafts may also be surgically implanted by anastomosis to replace a badly damaged portion of vessel.  
           [0005]    Vascular grafts may be manufactured from a variety of bio-compatible materials. For example, it is well known to use extruded tubes of polytetrafluoroethylene (PTFE) as vascular grafts. PTFE is particularly suitable as it exhibits superior biocompatibility. PTFE tubes may be used as vascular grafts in the replacement or repair of blood vessels because PTFE exhibits low thrombogenicity. Further, expanded PTFE (ePTFE) tubes have a microporous structure which allows natural tissue ingrowth and cell endothelialization once implanted into the vascular system. This contributes to long term healing and graft patency.  
           [0006]    Grafts formed of ePTFE have a fibrous state which is defined by interspaced nodes interconnected by elongated fibrils. The spaces between the node surfaces that are spanned by the fibrils are defined as the internodal distance (IND). The art is replete with examples of vascular grafts made of microporous ePTFE tubes useful as vascular grafts. The porosity of an ePTFE vascular graft is controlled by varying the IND of the microporous structure of the tube. An increase in the IND within a given structure results in enhanced tissue ingrowth, as well as, cell endothelialization along the inner surface thereof. Increasing the porosity of the tubular structure, however, reduces the ability of the graft to retain a suture placed therein during implantation and tends to exhibit low axial tear strength. In order to strike an effective balance between porosity and radial strength, multi-layer ePTFE tubes have been developed. The porosity of these multilayered tubes vary as between the outer and inner layers to achieve a composite structure having sufficient porosity for tissue ingrowth and cell endothelialization while still retaining sufficient radial strength.  
           [0007]    It is known in the art to use stents in combination with vascular grafts and other endoprostheses. Stents may be positioned at one or both ends of a graft to support the graft within a portion of the vessel. Thus positioned, the stents help fix the graft to the vessel wall. In addition, stents serve to keep the lumen open and to anchor the graft in place. A single stent may also be employed in combination with a graft to allow the graft to “float” downstream toward the affected vessel. Once properly positioned, the single stent is expanded to anchor the graft in place.  
           [0008]    Several techniques for securing one or more stents to a graft are known. For example, hooks or barbs extending from the stent have been used for securing stents to a graft. Alternatively, a stent may be sutured to a graft. Each of these techniques requires either specialized stent attachment means or secondary procedures to secure the stents to the graft.  
           [0009]    Traditional stents have various shapes and sizes depending upon their intended function. For example, structures which have previously been used as stents include coiled stainless steel springs, helically wound coiled springs manufactured from an expandable heat-sensitive material, expanding stainless steel stents formed of stainless steel wire in a “zig-zag” pattern, cage-like devices made from malleable metal, and flexible tubes having a plurality of separate expandable ring-like scaffold members which permit radial expansion of a graft. Each of these devices is designed to be radially compressible and expandable so that it will easily pass through a blood vessel in a collapsed state and can be radially expanded to an implantable size after the target area of the vessel has been reached. Radial expansion and contraction of each of these causes associated longitudinal expansion and contraction of the stent.  
           [0010]    Such expandable stents may be supported between the layers of a multi-layer tubular graft. The expandable stent would anchor and support the multi-layer tube within the lumen. Upon radial expansion, the stent would hold the graft outwardly against the inner wall of the lumen.  
           [0011]    One example of such a graft-stent combination is shown in U.S. Pat. No. 5,123,917 issued to Lee et al. A stent-graft combination shown therein includes a plurality of separate scaffold members (stents) mounted between an inner tube and an outer tube forming the multi-layer graft. In one embodiment of this invention, the scaffold members are free floating within an intermediate pocket formed by the inner and outer tubes. In another embodiment, the scaffold members are adhesively affixed to the outer surface of the inner tube. In yet another embodiment of this invention, the inner and outer tubes are adhered to each other in such a manner that separate pockets are formed in which individual scaffold members are placed within each pocket.  
           [0012]    In each of these different embodiments of the &#39;917 patent, radial expansion of the scaffold member causes a change in the longitudinal expanse thereof. Thus, a drawback to the device shown in the &#39;917 patent is that the net length of the scaffold member increases as the graft contracts. Accordingly, this increase in the net length of the scaffold member increases the stress forces on the graft as well as tends to delaminate the layers. Thus, these stress forces increase the likelihood that the inner tube will become separated from the outer tube and/or that the graft will tear upon expansion of the scaffold members.  
           [0013]    Accordingly, it would be desirable to provide an improved intraluminal device, in particular, an ePTFE graft-stent composite device with improved radial strength that allows for the deployment of a stent and graft simultaneously with the stent already permanently positioned on the graft such that additional stress is not placed on the graft by the stent upon expansion.  
         SUMMARY OF THE INVENTION  
         [0014]    In accordance with the present invention, an improved composite graft-stent device is provided. More particularly, the present invention is formed from two non thrombogenic tubes which are laminated or fused together with one or more stents secured therebetween. This composite device is then expanded to place it in intimate contact with the inner surface of the lumen in which it is positioned.  
           [0015]    The composite device is preferably an implantable intraluminal device with a first porous tube that has two opposed ends, an interior luminal surface and an exterior surface. The composite device also contains a second porous tube which is disposed concentrically about the exterior surface of the first tube and is secured to the exterior surface of the first tube. A radially expandable member is disposed about the exterior surface of the first tube and is longitudinally immobilized between the first and second tubes when they are secured. In the present invention, the second tube is secured to the first tube by fusion or by lamination.  
           [0016]    The radially expandable member between the two tubes includes a longitudinal expanse. As used herein, the term “longitudinal expanse” means the width of the radially expandable member as measured along the axis of the tube. In the present invention, when the member is expanded, there is no distortion along the longitudinal expanse of the member, e.g., the width remains constant as the member is expanded. The member is preferably an expandable stent.  
           [0017]    The expandable stent of the invention includes an elongated element with a first end and a second opposed end. In one embodiment of the invention, the elongated element is formed in a generally circular configuration with the first end adjacent to and overlapping the second opposed end. The stent is expandable through the relative movement of the first end with respect to the second opposed end.  
           [0018]    In another embodiment of the invention, the end extent of the first end of the elongated element has a plurality of second end engagement means for engaging the distal end of the second end to provide finite adjustability to the stent.  
           [0019]    In yet another embodiment of the present invention, the radially expandable stent includes an elongate element having a first end and a second opposed end. This elongate element is formed in a generally circular configuration with the first and second ends in axial alignment to each other. In this embodiment of the invention, the second end has an elongate open-ended channel wherein radial expansion is achieved by movement of the first end out of the open-ended channel of the second end.  
           [0020]    The implantable intraluminal device of the present invention is preferably fabricated out of a biocompatible metal. Most preferably, the implantable intraluminal device is stainless steel, platinum, gold, nitinol, tantalum and alloys thereof.  
           [0021]    The first and second tubes of the present invention are preferably fabricated out of a biocompatible material. Most preferably, the first and second tubes are fabricated out of expanded polytetrafluoroethylene (ePTFE).  
           [0022]    In the present invention, a stent may be disposed about the exterior surface of the first tube adjacent to either of the first or second ends. Alternatively, a stent may be disposed about the exterior surface of the first tube at both ends. In yet another embodiment, a plurality of stents may be disposed about the exterior surface of the fist tube and longitudinally spaced between stents located at the first and second ends of the device.  
           [0023]    In the present invention, the device may be expanded by an inflation force. Preferably, the inflation force is supplied by inflating a balloon catheter.  
           [0024]    The process of the present invention hereby incorporates by reference all of the limitations described above for the intraluminal implantable device. By way of summary, in the process of the invention an implantable intraluminal device is provided which includes a first luminal porous tube having first and second ends, an interior luminal surface and an exterior surface. One or more radially expandable members is/are then radially disposed about the exterior surface of the first tube. A second porous tube is then concentrically positioned over the first tube and the radially expandable member(s). The first tube is then secured to the second tube so that one or more expandable members is/are immobilized along the longitudinal axis of the first and second tubes. 
       
    
    
     BRIEF DESCRIPTION OF THE DRAWINGS  
       [0025]    The present invention can be further understood with reference to the following description in conjunction with the appended drawings, wherein like elements are provided with the same reference numbers. In the drawings:  
         [0026]    [0026]FIG. 1 is a longitudinal cross-section of the composite graft-stent of the present invention.  
         [0027]    [0027]FIG. 2 is a front view of the “key-ring” type stent employed in the composite graftstent of FIG. 1.  
         [0028]    [0028]FIG. 3 is a front view of another embodiment of a stent of the composite graft-stent of FIG. 1.  
         [0029]    [0029]FIG. 4 is a front view, partially in section of a still further embodiment of a stent of the composite graft-stent of FIG. 1. 
     
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT  
       [0030]    Now turning to FIG. 1, a longitudinal cross-section of the preferred embodiment of the graft-stent composite device  10  is shown. This device  10  includes a multilayer graft  25  which is formed of inner and outer tubes  12  and  22  that are preferably formed of expandable polytetrafluoroethylene (ePTFE). Although it is preferred that tubes  12  and  22  be made of ePTFE, any appropriate bio-compatible material, such as porous polyurethane, is also contemplated. Other potential materials for this application include DACRON, a proline mesh or the like. Ideally, the material should be inert and should not promote a significant amount of scar formation.  
         [0031]    Graft  25  has first and second opposed ends  14  and  16 , respectively. Tube  12  includes an exterior surface  18  and an interior luminal surface  20 . Tube  22  has an interior surface  24  and an exterior vascular surface  26 . Tube  22  is disposed concentrically over the exterior surface  18  of tube  12  to form the multilayer graft  25 .  
         [0032]    A plurality of longitudinally spaced stents  28  are disposed between the exterior surface  18  of tube  12  and the interior surface  24  of tube  22 . As will be described hereinbelow, each stent  28  is of the type which may be radially expanded. Stents  28  are longitudinally immobilized between tubes  12  and  22  when they are secured to each other. The stents  28  are positioned at spaced locations along the multi-layer graft  25  in numbers which may be selected based on use and application of the device  10 .  
         [0033]    [0033]FIG. 1 shows tubes  12  and  22  laminated together to form graft  25  with stents  28  disposed therebetween. Although FIG. 1 shows tubes  12  and  22  laminated together, any appropriate method of securement, such as fusion, is contemplated. The lamination of tubes  12  and  22  causes stents  28  to be immobilized along the longitudinal axis of the multi-layer graft  25 .  
         [0034]    Now turning to FIG. 2, a preferred embodiment of stent  28  is shown. Stent  28  may be formed from a wire  30  which is wound in the shape of a simple circle generally described as a “key-ring.” The circular wire  30  includes a first end  34  adjacent to and overlapping a second opposed end  36 . The wire  30  is radially expandable by movement of first end  34  and second end  36  in opposing directions relative to each other as indicated by arrow A. Radial expansion is accomplished by, for example, the expansion of a balloon catheter exerting radial pressure on wire  30 . This radial expansion is achieved without a change in the longitudinal expanse  32  of the wire  30  which is shown in FIG. 1. While balloon expansion is described, it is also contemplated that stent  28  may be of the self-expanding variety.  
         [0035]    Now with reference to FIG. 3, a further embodiment of the stent of the present invention is shown. Stent  28 ′ may be formed from a wire employing a simple “ratchet” design. The wire  30 ′ is formed in a circular configuration and includes a first end  34 ′ adjacent to and overlapping its second opposed end  36 ′. Several ratchet-like teeth  38 ′ are located at an end extent  40 ′ of the first end  34 ′. The other end  36 ′ includes a pawl  41 ′ at a distal end  42 ′ thereof for adjustable engagement with teeth  38 ′. Upon relative movement of opposed ends  34 ′ and  36 ′, teeth  38 ′ are engaged by pawl  41 ′ to provide adjustable interlocking therebetween. This allows the diameter of the circular stent  28 ′ to be adjustably expanded in incremental fashion, to set the diameter thereof at discrete increments.  
         [0036]    Now with reference to FIG. 4, an additional embodiment of a stent is shown. Stent  28 ″ is a wire stent employing telescoping-ends. The wire  30 ″ is formed in a circular configuration and includes a first end  34 ″ that is positioned in general axial alignment with a second opposed end  36 ″. A distal portion  34   a ″ of first end  34 ″ telescopes into an elongate open-ended channel  44 ″ formed at opposed end  36 ″. The diameter of the stent  28 ″ is contracted and expanded by movement of first end  34 ″ into and out of open-ended channel  44 ″.  
         [0037]    The various embodiments of each of the stents  28  described herein are preferably manufactured out of a bio-compatible metal. Most preferably, the bio-compatible metal is stainless steel, platinum, gold, nitinol, tantalum and alloys thereof.  
         [0038]    One or more such stents  28  may be disposed between tubes  12  and  22 . For example, in one embodiment a single stent  28  is disposed about one end of tube  12 . In an alternative embodiment of the invention, two stents  28  are disposed about each end of tube  12 . In yet another embodiment of the invention, several stents  28  are disposed about the exterior surface  18  of tube  12  and are longitudinally spaced therealong between the two ends  14  and  16  of tube  12 .  
         [0039]    While the preferred embodiments of the invention are shown and described below, other embodiments that fall within the scope of the disclosure and appended claims are also contemplated.  
         [0040]    The invention being thus described, it will be obvious that the same may be varied in many ways. Such variations are not to be regarded as a departure from the spirit and scope of the invention and all such modifications are intended to be included within the scope of the following claims.