ANTI-REFLUX ESOPHAGEAL PROSTHESIS

Abstract: An esophageal prosthesis (10) for preventing reflux of gastric fluids through the oesophagus. The esophageal prosthesis process includes a tubular frame (11) with a sleeve (13) disposed around and longitudinally along the tubular frame as well as extending from the distal end (14) of the frame. The lower portion (28) of the sleeve has a readily collapsible lumen (15) that forms a one-way valve for preventing the reflux of gastric fluids in an antegrade manner through the esophagus. Fluids however readily flow throuhgh the sleeve in a antegrade direction. In response to a pressurebuild up in the stomach of a patient wanting to belch or vomit, the lower portion of the sleeve inverts through the passage (12) of the tubular frame, thereby relieving the pressure build up or voiding the patient's stomach. The tubular frame includes a plurality (19) of self-expanding zig-zag wire stents (20, 21, and 23) that maintain the patency of the esophagus and, in particular, the lower esophageal sphincter and any tumor that is causing stricture of the esophagus.

Description: ANTI-REFLUX ESOPHAGEAL PROSTHESIS Description Technical Field This invention relates generally to medical devices and, in particular, to an anti-reflux esophageal prosthesis. Background of the Invention Anti-reflux esophageal prosthesis or stents are typically placed in the lower esophagus and through the lower esophageal sphincter to maintain the patency thereof due to the presence of a cancerous tumor commonly found in the vicinity thereof. The cancerous tumor growth typically impinges the flow of food and fluids through the esophagus. Lower esophageal cancer in the United States presently occurs at the rate of approximately 1 2,000 patients per year. The incidence in the United States is approximately 5.1 per 100,000 people, which is rising particularly in white male patients. Esophageal prosthesis or stents are typically utilized in these cancerous patients. However, these devices are not FDA approved for benign tumors which also cause blockage or partial stenosis of the esophagus. Esophageal prosthesis or stents are utilized in Europe and other countries for benign tumor conditions, but not in the United States at this time. A problem with esophageal prosthesis or stents is that fluid from the stomach flows into the mouth of the patient when in a prone position. In an attempt to solve this problem, a number of esophageal prosthesis or stents utilize a one-way valve such as a duck-bill or reed-type valve in which only food or fluid from the esophagus flows into the stomach in only an antegrade or forward direction. However, these one-way anti-reflux prosthesis or stents present another problem. When the patient wants to belch or vomit, he/she is prevented from doing so, because the one-way valve prevents backward flow in the retrograde direction. Such condition is not only painful to the patient, but can also lead to more complicated medical conditions. Summary of the Invention The foregoing problems are solved and a technical advance is achieved in an illustrative anti-reflux esophageal prosthesis in which a sleeve extending from a tubular frame thereof inverts through the passage of the tubular frame and allows stomach gas or vomit to flow in a retrograde direction when the pressure in the stomach exceeds a given level. In the antegrade or downward position, the sleeve collapses and prevents the reflux of stomach gas and fluid from flowing through the esophagus and into the mouth of the patient. The collapsible sleeve functions as a one-way valve and allows the patient to ingest or pass liquid and food therethrough and into the stomach. In addition, the tubular frame of this advantageous anti-reflux esophageal prosthesis maintains the patency of the lower esophagus and sphincter particularly when a cancerous tumor impedes fluid flow through the esophagus. In another advantageous aspect of the present invention, the tubular frame of the anti-reflux esophageal prosthesis includes a plurality of self-expanding zig-zag stents. The compressed stents along with the sleeve are positioned in an delivery catheter which is orally passed through the esophagus and lower sphincter. The prosthesis is then deployed from the delivery catheter with, for example, a dilator or pusher catheter that is inserted in the lumen of the delivery catheter. The deployed, self-expanding stents readily expand to engage the esophagus and lower sphincter and maintain them in a patent condition. The self-expanding stents of the tubular frame are also advantageously flared at each end of the tubular frame to prevent antegrade and retrograde migration of the expanded prosthesis. To further prevent migration of the zig-zag stents with respect to each other, a filament is circumferentially positioned through closed eyelets at the bends of adjacent zig-zag stents. The filaments are also utilized advantageously to control the radial expansion and the flared configuration of the stents positioned at the ends of the tubular frame. The pressure needed to collapse or invert the one-way valvular sleeve is a function of the sleeve material, its wall thickness and length extending from the distal end of the tubular frame. Depending on the anatomical size of the human or veterinary patient, the sleeve can extend from the end of the frame for a length in a range of from 0.0 to 20 cm, preferably in a range of 5 to 1 5 cm; and more preferably in length of approximately 10 cm in a human patient or 8 cm in a veterinary patient as experimentally derived therefor. The sleeve material also advantageously includes a material of polyurethane, silicone, polyamides, other urethanes or any biocompatible material that is flexible and acid resistant. The sleeve material can have an advantageous thickness of 0.005" through 0.008". This thickness is at the portion covering the frame itself. The sleeve extending from an end of the frame comprises a material having a thickness in a range of 0.001 5" to and including 0.004" and preferably approximately 0.002" . Advantageously, the length of the sleeve is made long enough so that it can be readily shortened to accommodate individual anatomical situations. Brief Description of the Drawing FIG. 1 depicts a pictorial view of an illustrative, preferred embodiment of a pressure sensitive anti-reflux esophageal prosthesis of the present invention; FIG. 2 depicts an enlarged sectioned end view of a sleeve about a cylindrical wire of a flared stent of the esophageal prosthesis of FIG. 1 along the line FIG. 3 depicts an enlarged partially sectioned view of the adjacent ends of interconnected stents of the prosthesis of FIG. 1 ; FIG. 4 depicts a two piece mandril that is used to apply the sleeve material to the prosthesis of FIG. 1 ; FIG. 5 depicts the esophageal prosthesis of FIG. 1 deployed in the lower esophagus of a patient, and, in particular, through the lower esophageal sphincter and a cancerous tumor; FIG. 6 depicts the anti-reflux esophageal prosthesis of FIG.1 in a collapsed state in a delivery catheter; FIG. 7 depicts the delivery catheter of FIG. 6 positioned in the lower esophagus, sphincter, and tumor of a patient; FIGs. 8 depicts an in-vitro barrier reflux curve for an anti-reflux esophageal prosthesis of the present invention; and FIGs. 9 and 10 depict the percent of fraction time of standard and anti- reflux esophageal prosthesis utilized in an evaluation of the present invention. Detailed Description FIG. 1 depicts a pictorial view of an illustrative, preferred embodiment of pressure sensitive anti-reflux esophageal prosthesis 10 of the present invention. The prosthesis includes a tubular frame 1 1 of a plurality 1 9 of self-expanding, zig-zag wire stents 20, 21 , and 23 covered by a polyurethane sleeve 1 3 that is disposed around and extends along entire length 27 of the tubular frame. The sleeve also extends from distal end 14 of the self-expanding tubular frame and has a lumen 1 5 extending longitudinally therethrough. Lumen 1 5 of the sleeve also communicates with passage 1 2 of the tubular frame. When the prosthesis is positioned in the lower esophagus and through the lower sphincter of a patient, lumen 1 5 in lower portion 28 of the sleeve collapses upon itself due to wetting by gastric juices, fluid or saliva flowing therethrough from the esophagus. As a result, sleeve 1 3 is in a collapsed position and acts as a one-way valve into the stomach, thereby preventing the reflux of gastric fluid from flowing in a retrograde manner through the prosthesis and esophagus and into the mouth of the patient. However, fluid readily flows in the opposite direction from the esophagus and through the one-way valve sleeve into the patient's stomach. Tubular frame 1 1 includes plurality 1 9 of self-expanding stents 20, 21 , and 23 that are interconnected circumferentially by filament 24 about adjacent ends 25 and 26 of the stents. In this illustrative embodiment, the tubular frame includes four self-expanding, zig-zag wire metal stents of the Gianturco type as described in U.S. Patent 4,580,568, which is incorporated by reference herein. Tubular frame includes first and second flared stents 20 and 21 positioned at distal and proximal ends 14 and 22 with first and second cylindrical stents 23 positioned therebetween. By way of example, first and second flared stents 20 and 21 have a minimum diameter of 1 8 mm and a flared diameter of approximately 25 mm. These diameters are nominal diameters for the stents and can be customized to meet the particular demands of any human or veterinary patient. The diameter of the flared end is maintained by end filament 29. The minimum diameter of the flared stents along with the nominal diameter of the cylindrical stents is maintained by interconnecting filaments 24. The interconnecting and end filaments 24 and 29 are, for example, 3/0 diameter mononylon suture material. The first and second flared stents 20 and 21 are positioned below and above the lower esophageal sphincter and prevent the migration of the prosthesis in either the antegrade or retrograde direction with respect to the esophagus. The flared proximal stent along with the cylindrical stents 23 also expand against any tumor that is in the region of the lower esophagus and maintains the patency of the lower esophageal lumen. Flared stents 20 and 21 are, for example, formed from commercially available Series 304 stainless steel cylindrical wire having a diameter of approximately 0.01 5". The wire is formed into a zig-zag pattern of which the ends are joined together using, for example, a metal sleeve and soldered together using silver/tin solder. However, other ways of forming a closed zig-zag configuration that resembles at least a partially tubular shape is contemplated. The flared or maximum diameter of the flared stents is approximately 25 mm with the minimum diameter at approximately 1 8 mm. Interconnecting cylindrical stents 23 are also formed from the same cylindrical wire and have a nominal diameter of approximately 1 8 mm matching that of the minimum diameter of the flared stents. The length of the individual stents is approximately 2 cm. The overall length of the tubular frame can range from 8 to 1 4 cm in 2 cm increments. These 2 cm increments are typically provided by increasing the number of interconnecting cylindrical stents 23. Sleeve 1 3 preferably comprises a polyurethane material or other liquid impermeable material that does not degrade in the presence of fluids or gastric material that comes in contact therewith. The sleeve is disposed around and extends at least partially around tubular frame 1 1 . Preferably, the sleeve extends the entire length of the frame and extends longitudinally from distal end 14 of the tubular frame. The length of the sleeve material extending from the distal end of the tubular frame can range from 0 through 20 cm, preferably 5 to 1 5 cm, and more preferably 10 cm. The length of the sleeve material can be individually customized by the physician depending on the anatomy of the patient. Experimental data has indicated that dogs typically utilize a 7 cm length of sleeve material. Human patients are expected to utilize a sleeve length of 8 or 9 cm. However, the length can again be modified by the physician to meet the particular anatomy of the patient. The wall thickness of the sleeve material disposed around the tubular frame is approximately 0.006" thick. The thickness of the sleeve material along lower portion 28 of the sleeve is approximately 0.002" thick. The sleeve material preferably includes a medical grade polyurethane material; although silicone, nylon, polyamides such as other urethanes, or other biocompatible material that is flexible and acid resistant are also suitable materials. In particular, the polyurethane of the present invention is a medical grade polyurethane material grade EG-80A material commercially known as TECOFLEX ® polyurethane material from Thermedics, Incorporated, Woburn, Massachusetts. FIG. 2 depicts an enlarged sectioned end view of sleeve 1 3 about cylindrical wire 30 of flared stent 20 of FIG.1 along the line 2-2. As shown, the thickness of the sleeve material is approximately 0.006", whereas the thickness of the sleeve material along lower or distal portion 28 thereof is preferably and approximately 0.002" . The thickness of sleeve material above distal portion 28 ranges from 0.005" through 0.008". Experimental data has indicated that the sleeve material along distal portion 28 still collapses at 0.004" wall thickness so as to effectively form a one-way valve. Closure of the one-way valve sleeve material occurs at thicknesses above 0.004"; however, closure does not occur on a guaranteed basis each time. The thickness of the sleeve wall material below 0.001 5" presents a problem of tearing particularly when inserting the prosthesis into a delivery catheter. FIG. 3 depicts an enlarged partially sectioned view of adjacent ends 25 and 26 of interconnected stents 20 and 23 of FIG. 1 . Bends 31 of cylindrical wire 30 are formed into a keyhole configuration with silver solder 32 interconnecting the wire arms, thereby forming an aperture or eyelet 33. Interconnecting filament 24 is positioned through each eyelet and wound around at least once to aid in fixing the diameter of the expandable stents. One interconnecting or end filament is used at the end of each stent and tied at the loose ends with suture knot 34. FIG. 4 depicts two piece mandril 35 that is used to apply sleeve material 13 to the prosthesis of FIG. 1 . The mandril includes sleeve portion 36 and upper frame portion 37 that are interconnectable with, for example, threaded rod 38 and internally threaded channel 39. In use, the tubular frame including the plurality of self-expanding wire stents are positioned end-to-end and interconnected using interconnecting filament 24. The end filament is also positioned through the eyelets of the flared stents to control the maximum diameter thereof. The mandril has a minimum inner diameter matching that of the inside diameter of the inner stents and a flared diameter matching that of the flared stents. Extending from the ends of the flared portions, the mandril assumes the inner diameter of the one-way valve sleeve material. The assembled tubular frame is positioned between the upper frame portion of the sleeve portion of the mandril. The two portions of the mandril are then interconnected, thereby filling up the passage of the tubular frame. The tubular frame is then dipped into a slurry material of polyurethane to form an initial 0.004" thickness over the entire length of the tubular frame. The mandril and covered tubular frame are then dipped in the slurry material at least one additional time to form the desired thickness of the sleeve material over mandril sleeve portion 36. After the slurry material cures, the two portions of the mandril are disconnected to form the anti-reflux esophageal prosthesis. FIG. 5 depicts esophageal prosthesis 10 deployed in lower esophagus 40, and, in particular, through lower esophageal sphincter 41 and cancerous tumor 42. Distal flared stent 20 typically extends into the stomach along with sleeve 1 3. Flared stent 21 is positioned proximal to the sphincter and tumor, whereas the interconnected cylindrical stents are typically positioned through the sphincter and tumor. The flared stents 20 and 21 , again, prevent a migration of the prosthesis in the esophagus. The lower or distal portion 28 of sleeve 1 3 extends into stomach 43. The lumen of the lower sleeve portion readily collapses when in contact with any external fluid applied thereto. However, any liquid or food is readily passed in an antegrade direction through the esophageal stent and into the stomach. As a result, one-way valve sleeve 1 3 opens to provide flow in the antegrade direction. Conversely, any fluids or food material 44 are prevented from flowing into the retrograde direction due to the collapsed lumen of sleeve 1 3. However, when the pressure of the gas or fluid in the stomach builds so as to cause the patient to belch or vomit, sleeve 1 3 will invert and extend in an antegrade direction through the lumen of the tubular frame as shown by phantom lines 45. In this position, gastric fluid and matter flows in the retrograde direction to relieve the patient. The length of distal portion 28 of the sleeve and the thickness thereof control the pressure at which the distal portion of the sleeve inverts through the tubular frame. Self-expanding esophageal prosthesis are increasingly being used for palliation of malignant dysphagia. They can predispose to significant gastroesophageal reflux, including risk of aspiration, when deployed across the gastroesophageal junction. A study was performed to evaluate the anti-reflux efficacy of a esophageal prosthesis of the present invention to prevent reflux. A model EZS 21 -8 from Wilson-Cook Inc., Salem, NC ( 1 6 mm diameter) was modified by extending its polyurethane covering 7 cm beyond its distal metal cage so as to form a "windsock" or collapsible sleeve. The pressure required to invert the windsock or collapsible sleeve into the tubular frame (reflux barrier) was determined by attaching the proximal end of the prosthesis to a hollow graduated tube and vertically inserting the stent under water until the windsock inverted. The pressure required to revert the windsock or collapsible lumen to its original one-way position was determined by pouring water into the lumen of the prosthesis. In-vivo evaluation was done in two esophagostomized dogs (male -1 8 kg, female - 1 6 kg) and prosthesis insertion, positioning, and removal done by standard endoscopic and fluoroscopic techniques. Two site ambulatory esophageal pH monitoring (Synectics Medical) was performed at 5 c m and 10 cm above the gastroesophageal function. Each dog was studied twice using the standard model EZS 201 -8 prosthesis and twice using the modified prosthesis (mean recording time per session 1 8.7 + /- 1 SE and 1 7 + /- 3 hours respectively). The results indicated that the windsock modification posed no difficulty in mounting or deploying the prosthesis using a currently available delivery system. Resistance to antegrade flow was minimal as even a drop of water put into the prosthesis easily passed through the windsock and both the dogs drank all the Ensure (4 cans per session) given to them irrespective of the type of prosthesis used. The pressure (cm of water) to overcome the reflux barrier was 1 5.7 + /- 0.3 SE and that to revert an inverted windsock or collapsible lumen was 0.4 + /- 0.03 SE. Results of the pH monitoring (mean + /- SE) is depicted in Table 1 . Table 1 The conclusions reached in the experiment were that a modified self- expanding metal esophageal prosthesis is highly effective in preventing reflux. The ability of the windsock or collapsible lumen sleeve 1 3 to invert at higher pressure gradients can allow patients to belch or vomit. Reversion to anti-reflux position requires minimal pressure and can be achieved by a water swallow. Further studies are indicated in FIGs. 8 - 1 7. FIG. 6 depicts anti-reflux esophageal prosthesis 10 of FIG. 1 in a collapsed state in delivery catheter 46. Sleeve material 1 3 is positioned at the distal end of the delivery catheter. The prosthesis is drawn into the delivery catheter with a drawstring attached at the proximal end of the prosthesis. The drawstring and prosthesis are inserted through lumen 47 of the catheter by collapsing the tubular frame and then pulling the prosthesis into the distal end of the delivery catheter with the drawstring. To deploy the collapsed prosthesis from the delivery catheter, a pusher catheter 48 is positioned proximally in lumen 47 to engage the proximal end of the wire tubular frame 1 1 . FIG. 7 depicts delivery catheter 46 of FIG. 6 positioned in lower esophagus 40, sphincter 41 , and tumor 42 of a patient. The distal end of the delivery catheter extends into stomach 43. As shown, the pusher has been placed in the lumen of the delivery catheter and engages the proximal end of prosthesis 10. As shown, sleeve 1 3 and flared distal stent 20 have been deployed from the distal end of the catheter. After the sleeve and distal flared stent 20 of the prosthesis have been deployed, the delivery catheter is partially withdrawn so as to engage the flared stent with the neck of the stomach about sphincter 41 . Once positioned, the delivery catheter is pulled back while maintaining the position of the pusher catheter therein so as to release the central cylindrical stents and proximal flared stent against the sphincter, tumor, and lower esophagus. An in-vitro and in-vivo evaluation of a modified self-expandable metal esophageal stent with an anti-reflux mechanism of the present invention was performed on a number of dogs. The evaluation included four dogs, two of which were males at 14 and 1 8 kg and two females at 1 4 and 1 6 kg. An esophagostomy was utilized with the use of upper gastro-intestinal endoscopy. The evaluation included the methods of ambulatory pH monitoring with the use of Synectics medical equipment at 5 and 10 cm with Gastrograph Inc. software. A liquid diet of Ensure at a pH of 6.5 was administered. The results of the employed methods are included in Table 2. Table 2 FIG 8 depicts in-vitro reflux barrier curve 48 which illustrates the water column height in centimeters necessary to invert a given sleeve length extending from the distal end of the prosthesis. Rectangular median value boxes 49 indicate the median value of the water column height at the indicated sleeve lengths. The vertical bar 50 positioned on curve 48 with rectangular median value boxes 49 represent a standard deviation above and below the indicated median value. In addition, the number of reflux episodes was monitored at the distal and proximal ends of the prosthesis. With a standard prosthesis without a one way valve, 1 97 episodes of reflux were encountered in 250 attempts. At the proximal end of the standard tubular esphageal prosthesis, a total of 33 reflux episodes were noted with 50 attempts. Correspondently, only 1 6 reflux episodes were noted out of 250 attempts at the distal end of an anti-reflux esophageal prosthesis of the present invention. At the proximal end of the anti-reflux esophageal stent only 8 episodes out of 50 attempts were noted. The number of reflux episodes longer than five minutes was also noted. In the standard prosthesis, 1 9.8 episodes were recorded for 25 attempts. This is in contrast to 0.3 episodes for an anti-reflux esophageal stent of the present invention. At the proximal end of the prosthesis, 2.3 episodes lasting longer than five minutes were noted with three attempts; whereas none were noted with the anti-reflux prosthesis. The longest reflux episodes were also noted at the distal and proximal ends of the standard and anti-reflux prosthesis. For the standard prosthesis, 1 07 episodes were noted out of approximately 1 30 attempts; whereas only 3.8 were noted for the anti-reflux prosthesis at the distal end thereof. At the proximal end of the prosthesis, 39 episodes were noted out of 45 for the standard prosthesis; whereas only 1 .8 for the anti-reflux prosthesis were noted. FIG 9 depicts the fraction time percentages of which the esophagus was exposed to gastric juice with a pH less than 4. At the distal end of the prosthesis, the percentage of fraction time is indicated by boxes 51 for the four dogs at the distal end of the standard prosthesis. These percentage fraction times range from 20-80% with a median value of 49%. For the anti-reflux prosthesis, the percentage of fraction time ranges from 0.0 to approximately 1 .5% with a median value of 1 % as indicated by boxes 52. The p-values for these fractions times is 0.026. FIG 1 0 depicts the fraction time percentages at the proximal ends of the standard and anti-reflux prosthesis. Boxes 53 represent the percent fraction time for the standard prosthesis which ranges from approximately 4-14% with a median of 6.6%. Rectangular boxes 54 represent the percent fraction time for the anti-reflux prosthesis which range from approximately 0.0 to 1 .0%. These have a p-value of approximately 0.055. The conclusions resulting from this in-vitro and in-vivo evaluation are as follows. The modified self-expanding metal esophageal stent of the present invention is highly effective in preventing gastro-esophageal reflux. The ability of the modification to invert at higher pressure gradients allows for belching and vomiting. Once inverted, reversion to the anti-reflux position of the prosthesis requires minimal pressure that can be achieved by a water swallow. It is to be understood, however, that the above described anti-reflux esophageal prosthesis is merely an illustrative embodiment of this invention, and that other devices and methods for manufacturing and using them may be devised by those skilled in the art without departing from the spirit and scope of the invention. It is also to be understood that the invention is directed to embodiments both comprising and consisting of disclosed parts. It is contemplated that only a portion of the tubular frame need be coated with the sleeve material. Furthermore, the sleeve material extending from the distal end of the tubular frame can be formed with different material from that covering the tubular frame. It is also contemplated that the material of the stents of the self-expanding stents can be formed of other materials such as nickel titanium alloys commercially known as nitinol, spring steel, and any other spring-like material formed to assume the flexible self-expanding zigzag stent configuration.

Claims: Claims 1 . An anti-reflux esophageal prosthesis (10) comprising of a tubular frame (1 1 ) having a passage (1 2) extending longitudinally therethrough and a sleeve (1 3) disposed around and extending at least partially along said tubular frame, said sleeve extending from an end (14) of said frame and having a lumen ( 1 5) extending longitudinally therethrough and communicating with said passage of said frame, said sleeve in response to a fluid (1 6) applying a first pressure in a first direction (1 7) passing the fluid through said lumen thereof, said sleeve collapsing in response to a fluid applying a second pressure in a second direction (1 8). 2. The prosthesis of claim 1 , wherein said sleeve extends through said passage of said tubular frame in response to a fluid applying a third pressure greater than said second pressure. 3. The prosthesis of claim 1 , wherein said tubular frame includes a plurality of stents (1 9) disposed along said tubular frame, said sleeve being disposed around at least one of said stents. 4. The prosthesis of claim 3, wherein said plurality of stents includes a first flared stent (20) disposed about said end of said frame. 5. The prosthesis of claim 4, wherein said plurality of stents includes a second flared stent (21 ) disposed about an other end (22) of said frame. 6. The prosthesis of claim 5, wherein said plurality of stents includes at least one cylindrical stent (23) disposed between said first and said second flared stents. 7. The prosthesis of claim 3, wherein said plurality of stents includes self- expanding stents (20, 21 , and 23). 8. The prosthesis of claim 1 , wherein said tubular frame includes a plurality of self-expanding stents (1 9-21 , and 23). 9. The prosthesis of claim 8, wherein at least one of said plurality of self- expanding stents includes a zig-zag stent. 10. The prosthesis of claim 9, wherein said tubular frame includes a filament (24) interconnecting adjacent ends (25, 26) of said plurality of self-expanding stents. 1 1 . The prosthesis of claim 8, wherein at least one of plurality of self- expanding stents includes a zig-zag wire stent. 1 2. The prosthesis of claim 1 , wherein said sleeve extends longitudinally along an entire length (27) of said tubular frame. 1 3. The prosthesis of claim 1 , wherein said sleeve extends from said end of said frame for a length in a range of from 0 through 20 cm. 1 4. The prosthesis of claim 1 , wherein said sleeve extends from said end of said frame for a length in a range of from 5 through 1 5 cm. 1 5. The prosthesis of claim 1 , wherein said sleeve comprises a material from at least one of a group consisting of polyurethane, silicone, polyamides, other urethanes or any biocompatible material that is flexible and acid resistant. 1 6. The prosthesis of claim 1 , wherein said sleeve disposed around and extending at least partially along said frame comprises material having a thickness in a range of 0.005" through 0.008". 1 7. The prosthesis of claim 1 , wherein said sleeve extending from said end of said frame comprises a material having a thickness in a range of 0.001 5" to and including 0.004". 1 8. The prosthesis of claim 1 , wherein said extending from said end of said frame comprises a material having a thickness of approximately 0.002" .

Inventors: DUA KULWINDER S, MOORE SCOTT T, DUA, KULWINDER, S., MOORE, SCOTT, T.
Applicants: WILSON COOK MEDICAL INC, WILSON-COOK MEDICAL INC.
Application year: 1999
Main classification: A61F2
IPC codes: A61F2