|Publication number||USRE42244 E1|
|Application number||US 10/875,088|
|Publication date||22 Mar 2011|
|Filing date||23 Jun 2004|
|Priority date||23 Jul 1993|
|Also published as||CA2144305A1, CA2144305C, DE69330132D1, DE69330132T2, EP0662806A1, EP0662806B1, US5632771, US6409752, WO1995003010A1|
|Publication number||10875088, 875088, US RE42244 E1, US RE42244E1, US-E1-RE42244, USRE42244 E1, USRE42244E1|
|Inventors||Scott E. Boatman, Kimberly D. Roberts|
|Original Assignee||Cook Incorporated|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (70), Referenced by (3), Classifications (12), Legal Events (4)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This is a reissue of application Ser. No. 08/748,669, now U.S. Pat. No. 6,409,752 B1, which is a continuation of Ser. No. 08/378,073 filed on Jan. 25, 1995 now U.S. Pat. No. 5,632,771 which is a file wrapper continuation of Ser. No. 08/097,392 filed on Jul. 23, 1993, now abandoned.
This invention relates generally to balloon expandable stents and, in particular, to a flexible stent having a waveform pattern formed from a sheet of biocompatible material and into a cylindrical surface or tubular shape. References herein to forming the stent from a “sheet” or “sheets” describe preferred embodiments of the invention, and are not to be construed to limit the claims.
Vascular stents are deployed at a narrowed site in a blood vessel of a patient for widening the vessel lumen and circumferentially supporting the vessel wall. Vascular stents desirably present a small cross-sectional dimension or profile for introducing the stent into the affected vessel lumen.
One approach to providing a vascular stent is the use of a piece of wire bent into a number of turns. Although suitable for its intended use, a problem with these bent wire stents is that stress points are formed at each wire bend or turn. As a result, the wire stent is structurally compromised at a number of points. Furthermore, bent wire stents lack longitudinal stability. For example, a wire stent is typically positioned in a blood vessel over an inflatable balloon. The balloon expands first at opposite ends, where the balloon is not in contact with the wire stent. As a result, the wire stent is longitudinally compressed between the inflated balloon ends. With continued inflation, the middle of the balloon expands, thereby unevenly expanding the wire bends of the longitudinally compressed wire stent. In an attempt to remedy the problem, the stent wire material has been formed to cross over or attach to itself. A problem with this attempted remedy is that the cross-sectional dimension of the stent, or stent profile, is increased, and the stent intrudes into the effective lumen of the blood vessel. The effective lumen of the blood vessel is further constricted by the growth of endothelial tissue layers over the stent wire. As a result, the stent and tissue growth impede fluid flow and cause turbulence in the vessel lumen. Another problem with this attempted remedy is that galvanic action, exposure to a reactive surface, or ion migration, occurs at the wire-to-wire contact points. The wire stent material rubs when movement occurs during ordinary blood flow and pulsation as well as patient muscle movement.
Another approach to providing a vascular stent is the use of a piece of metal cannula with a number of openings formed in the circumference thereof. A problem with the use of a metal cannula stent is that the stent is rigid and inflexible. As a result, the stent is difficult, if not impossible, to introduce through the tortuous vessels of the vascular system for deployment at a narrowed site. Furthermore, the stent is too rigid to conform with a curvature of a blood vessel when deployed at an occlusion site. Another problem with the use of a metal cannula stent is that the stent longitudinally shrinks during radial expansion. As a result, the position of the metal cannula stent shifts, and the stent supports a shorter portion of the blood vessel wall than anticipated merely by stent length.
Yet another approach to providing a vascular stent is the use of a wire mesh that is rolled into a generally tubular shape. A problem with the use of a wire mesh stent is that the overlapping wires forming the mesh increase the stent profile, thereby reducing the effective lumen of the blood vessel. The growth of endothelial tissue layers over the wire mesh further reduces the effective blood vessel lumen. Another problem with this approach is that ion migration also occurs at the wire-to-wire contact points.
Still yet another approach to providing a vascular stent is the use of a flat metal sheet with a number of openings formed in rows therein. The flat metal sheet stent also includes three rows of fingers or projections positioned on one edge of the stent along the axis thereof. When expanded, a row of the fingers or projections is positioned through a row of openings on the opposite edge is of the stent for locking the expanded configuration of the stent. A problem with the use of the flat metal sheet stent is that the overlapping edges of the stent increase the stent profile. Again, the stent profile and endothelial growth reduce the effective blood vessel lumen. Another problem with the use of the flat metal sheet stent is that the fingers or projections along one edge of the stent make wire-to-wire contact with the opposite edge of the stent. As a result, the metal edges of the stent rub during movement caused by blood flow, pulsation, and muscle movement. Yet another problem with the use of the flat metal sheet stent is that the fingers or projections extend radially outwardly and into the vessel wall. As a result, the intimal layer of the vessel wall is scraped, punctured, or otherwise injured. Injury and trauma to the intimal layer of the vessel wall result in hyperplasia and cell proliferation, which in turn effect stenosis or further narrowing of the vessel at the stent site.
The foregoing problems are solved and a technical advance is achieved in an illustrative embodiment of a flexible stent comprising a waveform pattern that is formed from a sheet of malleable, biocompatible material having a specified uniform thickness. The pattern is formed into a tubular shape and into an overlapping state around a delivery catheter balloon for introduction through tortuous vessels to, for example, an occlusion site in a coronary vessel. To provide longitudinal flexibility while preventing longitudinal contraction or expansion of the stent during radial expansion of the stent, the pattern advantageously includes a reinforcing member extending longitudinally therealong. A plurality of cells extends laterally from the reinforcing member with selected of the closed cells each having a fixedly sized aperture therein. The closed cells are interposed when the stent is in the tubular shape. To minimize the thickness of the stent and the growth of endothelial cells therearound, each segment of the cells extends laterally from the reinforcing member and does not overlap itself or any adjacent laterally extending segment of the cells. The sheet of biocompatible material with the pattern formed therein is formed into a radially alterable tubular shape around a delivery catheter balloon for introduction to the occlusion site. The balloon radially expands the stent to engage the vessel wall surface and to maintain the vessel lumen in an open condition. The expanded stent in a nonoverlapping state advantageously has a minimal thickness for endothelial tissue to form thereover. As a result, the vessel lumen is advantageously maintained with the largest diameter possible.
The pattern of the stent when in the tubular shape includes an overlapping state in which at least one segment of the selected cells overlaps the reinforcing member and forms a combined thickness with and along the reinforcing member of no more than substantially twice the thickness of the sheet of material. A deflated, delivery catheter balloon is positioned within the tubular-shaped stent to radially expand the stent to a nonoverlapping, expanded state when positioned at the occlusion site. The outermost longitudinal edges of the tubular stent move radially and circumferentially relative to each other when the stent is being radially altered. These outermost edges advantageously engage the surface of the lumen wall to maintain the stent in the expanded state. These outermost edges are most evident on the curved end segments of the interposed cells of the pattern when in the tubular shape. To aid expansion of the stent with the delivery balloon, the stent surface material is treated to lower its coefficient of friction. In one instance, the treatment comprises a coating of parylene on the surface of the sheet of material. Other coating materials include polytetrafluoroethylene. Furthermore, the surface of the stent may be ion beam bombarded to advantageously change the surface energy density and the coefficient of friction.
To maintain the moment of inertia or stiffness of the stent, each segment of the cells has a width substantially greater than the specified thickness of the sheet material. Increasing the width of the laterally extending segments also increases the surface area of the stent and support of the vessel wall.
To increase the expansion ratio of the stent, the laterally extending cells may be formed around the reinforcing member more than once and within the aperture of a closed cell without each segment overlapping itself or any adjacent cell segment. The width of the cell along the reinforcing member is advantageously selected so that each laterally extending segment forms a predetermined angle so as not to overlap itself or any adjacent cell segment. This is to advantageously maintain a combined thickness with and along the reinforcing member of no more than substantially twice the thickness of the sheet of material.
Radiopaque markers are advantageously positioned at one or more ends of the waveform pattern to aid the physician in positioning the stent at the occlusion site.
The method of making the balloon expandable stent includes the steps of providing a sheet of malleable material having an initial surface area and removing a majority of the material so that the sheet becomes a framework of integrated support members having a small surface area relative to the initial surface area of the sheet of material.. The method also includes positioning the framework around a cylindrical mandrel so that the framework defines at least a partially cylindrical surface or tubular shape. The removing step also includes removing isolated portions of the sheet so that the framework includes a plurality of closed cells bounded by the integrated support members. The removing step is also carried out so that the framework has a fixed length despite a reduction or expansion of the radius of the cylindrical surface or tubular shape. The cylindrical surface or tubular shape has a longitudinal axis and a substantially circular cross-section. The removing step is carried out so that the cylindrical surface or tubular shape is sufficiently flexible about the longitudinal axis to adapt the stent to curved passages within a body vessel without significantly altering the circular cross-section.
The stent of the present invention may also be characterized as a sheet of malleable material which has had a portion of the material removed so that the sheet becomes a framework of integrated support members arranged around a longitudinal axis to define a cylindrical surface. The cylindrical surface has a reduced diameter for delivery of the stent into a passage within a body vessel. The cylindrical surface is also plastically expandable from the reduced diameter to an expanded diameter for holding the passage open. The cylindrical surface has a range of diameters between the reduced diameter and the expanded diameter that are free from overlapping material. Each of the support members of the stent has a width and a thickness significantly less than the width. The support members are integrated in a way that the framework maintains a fixed length when the cylindrical surface is expanded from the reduced to the expanded diameter. One of the support members is a reinforcing member that extends from a first to a second end of the stent. The remaining support members extend laterally on each side of the reinforcing member. The cylindrical surface of the stent also defines a cylindrical surface when expanded to the expanded diameter. In addition, the cylindrical surface is sufficiently flexible about the longitudinal axis so that the stent can advantageously adapt to curved passages within a body vessel without significantly altering its circular cross section. The framework of the stent also includes a plurality of closed cells bounded on all sides by the integrated support members.
Pattern 13 includes a reinforcing member 14 extending longitudinally between opposite ends 15 and 16 for providing longitudinal stability thereof, particularly during radial expansion of the stent in the body passage. The length of prior art stents that are formed from a tube typically shorten as the stent is radially expanded. When formed into a tubular shape, pattern 13 includes a plurality of interposed closed cells 17-19 that extend laterally from the reinforcing member for providing vessel wall support. The tubular shaped pattern also exhibits longitudinal flexibility for introducing the stent through tortuous vessels to, for example, a coronary artery. Unlike a wire stent in which a wire is bent into a waveform pattern, waveform pattern 13 is formed from a flat sheet of material without any stresses being introduced at the curved segments thereof. As a result, thickness 23 of stent 10, as well as sheet 11, can be made extremely thin in comparison to that of a wire stent to minimize endothelial tissue buildup in the vessel. The same well-known moment of inertia or stillness of a wire stent is maintained by adjusting the width of each pattern member segment for a given sheet thickness.
When stent 10 is positioned in the overlapping state around a deflated catheter balloon, any segment of a laterally extending cell that overlaps the reinforcing member only forms a combined thickness 29 with and along the reinforcing member of no more than substantially twice the thickness of the sheet material. Accordingly, the stent is formed with an extremely small outside diameter while maximizing the inside diameter of the stent for receiving the delivery catheter balloon. When the stent is expanded in a blood vessel, the tubular shape is radially altered from a reduced, minimal inside diameter to an expanded diameter for holding the blood vessel open. In addition, oppositely facing, outermost longitudinal edges 20 and 21 of the pattern move radially and circumferentially relative to each other so that the pattern in the sheet of material is not stressed or deformed in the plane of the sheet of material. The substantially cylindrical surface of the tubular shape has a range of diameters between the expanded diameter and the reduced diameter for holding the vessel open in which the interposed cells are free of overlapping sheet material. The pattern is integrated in such a way that the framework thereof maintains a fixed length when the cylindrical surface of the tubular shape is expanded from the reduced diameter of the overlapping state to a larger diameter.
Interposed cell 17 includes fixedly sized aperture 22 with segments 24-26 and reinforcing member 14 disposed around the aperture. Substantially straight segments 24 and 25 extend laterally from reinforcing member 14, and curved segment 26 interconnects straight segments 24 and 25. Straight segments 24 and 25 are positioned circumferentially around the tubular shape in the space of aperture 22 without overlapping themselves or other adjacent cell segments for minimizing the stent profile or thickness in the overlapping state. Straight segments 24 and 25 extend laterally from the reinforcing member at angles 27 and 28, for example, both slightly acute at 82-83 degrees. Therefore, as depicted in
Pattern 13 is formed from sheet 11 of biocompatible material by photochemically etching, stamping, laser cutting, or any other of a number of well-known methods. Forming pattern 13 in a thin sheet of material provides a stent with an increased vessel contact surface area without increasing the metal mass of the stent, which is a limitation of prior art wire stents. A stent with an expanded inside diameter of 3 mm, for example, is formed from a sheet of material approximately 0.371″ wide, 0.7865″ long, and 0.003″ thick. Reinforcing member 14 and straight segments 24 and 25 are approximately 0.012″ wide. Curved segment 26 has a 0.010″ inside radius along oppositely facing, outermost edges 20 and 21. Reinforcing member 14 is positioned along the centerline of pattern 13 and has a .005″ radius at intersections with the straight segments of the interposed cells. Centerlines through apertures 22 and 50 transverse to the reinforcing member are positioned 0.143″ apart. Opposite stent ends 15 and 16 have a 0.017″ radius formed thereon defining projections that extend therefrom to free ends to define the furthest extents of the unopposed proximal and distal ends of the stent, and the projections include openings (see
A method of making balloon expandable stent 10 includes providing a sheet 11 of material with an initial surface area 43 and removing a majority 44 of the sheet material so that the remaining sheet 49 becomes a framework of integrated support members such as waveform pattern 13 having a small surface area relative to the initial surface area. The method also includes positioning the framework around a cylindrical mandrel so that the framework defines a cylindrical surface 34 or tubular shape 12. The cylindrical surface has a radius that can be expanded or reduced; however, the length of the surface and stent remains fixed despite a reduction or expansion of the radius. Cylindrical surface 34 also has a longitudinal axis and a substantially circular cross section. The surface is sufficiently flexible about the longitudinal axis so that the stent can adapt to curved passages within a body vessel without significantly altering the circular cross section. By way of example, the material removed from sheet 11 to form stent 10 includes isolated portions 45 and 46 resulting in respective apertures 22 and 47 for providing respective closed cells 17 and 18, each bounded by integrated support members such as straight segments 24 and 25, interconnecting curved segment 26, and reinforcing member 14. The stent framework is formed into at least a partially cylindrical or U-shaped surface with, for examples cylindrical mandrel 38 and U-shaped form 48 as depicted in
5 shown. The cylindrical mandrel is removed, and a delivery catheter balloon inserted in the U-shaped stent. The stent is then formed into cylindrical surface 34 or tubular shape 12 around the delivery catheter balloon with the aid of U-shaped form 48 forming the U-shaped interposed cells around the balloon and into the cylindrical surface or tubular shape. Well-known pulling tools with hooks at the ends thereof can be used to engage the interposed cells to pull the cells tightly around the delivery catheter balloon. These pulling tools are disclosed with a very similar forming method in U.S. Pat. No. 4,907,336 of Gianturco, which is incorporated by reference herein.
It is to be understood that the above-described stent is merely an illustrative embodiment of the principles of this invention and that other stents may be devised by those skilled in the art without departing from the spirit and scope of this invention. It is contemplated that any overlapping state stent formed from a sheet of material to minimize endothelial tissue growth is within the spirit and scope of this invention. Any equivalent shape of the waveform as illustrated by the preferred and alternative embodiments of the stent is also contemplated.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3868956||5 Jun 1972||4 Mar 1975||Ralph J Alfidi||Vessel implantable appliance and method of implanting it|
|US4323071||19 May 1980||6 Apr 1982||Advanced Catheter Systems, Inc.||Vascular guiding catheter assembly and vascular dilating catheter assembly and a combination thereof and methods of making the same|
|US4332254||17 Nov 1980||1 Jun 1982||Advanced Catheter Systems, Inc.||System for filling and inflating and deflating a vascular dilating cathether assembly|
|US4345602||29 Jan 1980||24 Aug 1982||Toray Monofilament Company Limited||Medical vascular guide wire and self-guilding type catheter|
|US4439185||21 Oct 1981||27 Mar 1984||Advanced Cardiovascular Systems, Inc.||Inflating and deflating device for vascular dilating catheter assembly|
|US4468224||28 Jan 1982||28 Aug 1984||Advanced Cardiovascular Systems, Inc.||System and method for catheter placement in blood vessels of a human patient|
|US4512338||25 Jan 1983||23 Apr 1985||Balko Alexander B||Process for restoring patency to body vessels|
|US4516972||12 Aug 1983||14 May 1985||Advanced Cardiovascular Systems, Inc.||Guiding catheter and method of manufacture|
|US4538622||10 Nov 1983||3 Sep 1985||Advanced Cardiovascular Systems, Inc.||Guide wire for catheters|
|US4553545||15 Sep 1982||19 Nov 1985||Medinvent S.A.||Device for application in blood vessels or other difficultly accessible locations and its use|
|US4554929||13 Jul 1983||26 Nov 1985||Advanced Cardiovascular Systems, Inc.||Catheter guide wire with short spring tip and method of using the same|
|US4569347||30 May 1984||11 Feb 1986||Advanced Cardiovascular Systems, Inc.||Catheter introducing device, assembly and method|
|US4571240||12 Aug 1983||18 Feb 1986||Advanced Cardiovascular Systems, Inc.||Catheter having encapsulated tip marker|
|US4572186||7 Dec 1983||25 Feb 1986||Cordis Corporation||Vessel dilation|
|US4616652||19 Oct 1983||14 Oct 1986||Advanced Cardiovascular Systems, Inc.||Dilatation catheter positioning apparatus|
|US4655771||11 Apr 1983||7 Apr 1987||Shepherd Patents S.A.||Prosthesis comprising an expansible or contractile tubular body|
|US4680031||24 Oct 1984||14 Jul 1987||Tascon Medical Technology Corporation||Heart valve prosthesis|
|US4681110||2 Dec 1985||21 Jul 1987||Wiktor Dominik M||Catheter arrangement having a blood vessel liner, and method of using it|
|US4693721||22 Apr 1986||15 Sep 1987||Paul Ducheyne||Porous flexible metal fiber material for surgical implantation|
|US4723549||18 Sep 1986||9 Feb 1988||Wholey Mark H||Method and apparatus for dilating blood vessels|
|US4733665||7 Nov 1985||29 Mar 1988||Expandable Grafts Partnership||Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft|
|US4739762||3 Nov 1986||26 Apr 1988||Expandable Grafts Partnership||Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft|
|US4748982||6 Jan 1987||7 Jun 1988||Advanced Cardiovascular Systems, Inc.||Reinforced balloon dilatation catheter with slitted exchange sleeve and method|
|US4748986||29 Jan 1987||7 Jun 1988||Advanced Cardiovascular Systems, Inc.||Floppy guide wire with opaque tip|
|US4762128||9 Dec 1986||9 Aug 1988||Advanced Surgical Intervention, Inc.||Method and apparatus for treating hypertrophy of the prostate gland|
|US4790315||2 Sep 1986||13 Dec 1988||Advanced Cardiovascular Systems, Inc.||Perfusion dilatation catheter and method of manufacture|
|US4800882||13 Mar 1987||31 Jan 1989||Cook Incorporated||Endovascular stent and delivery system|
|US4812120||2 Nov 1987||14 Mar 1989||Flanagan Dennis F||Implantable percutaneous device|
|US4848342||10 Sep 1986||18 Jul 1989||Martin Kaltenbach||Dilation catheter|
|US4877030||31 May 1988||31 Oct 1989||Andreas Beck||Device for the widening of blood vessels|
|US4892541||29 Jan 1987||9 Jan 1990||Tascon Medical Technology Corporation||Heart valve prosthesis|
|US4893623||20 Nov 1987||16 Jan 1990||Advanced Surgical Intervention, Inc.||Method and apparatus for treating hypertrophy of the prostate gland|
|US4907336||9 Sep 1988||13 Mar 1990||Cook Incorporated||Method of making an endovascular stent and delivery system|
|US4969458||6 Jul 1987||13 Nov 1990||Medtronic, Inc.||Intracoronary stent and method of simultaneous angioplasty and stent implant|
|US4969890||7 Jul 1988||13 Nov 1990||Nippon Zeon Co., Ltd.||Catheter|
|US5007926||24 Feb 1989||16 Apr 1991||The Trustees Of The University Of Pennsylvania||Expandable transluminally implantable tubular prosthesis|
|US5019090 *||1 Sep 1988||28 May 1991||Corvita Corporation||Radially expandable endoprosthesis and the like|
|US5030233 *||17 Jul 1987||9 Jul 1991||Paul Ducheyne||Porous flexible metal fiber material for surgical implantation|
|US5032113 *||13 Apr 1989||16 Jul 1991||Scimed Life Systems, Inc.||Innerless catheter|
|US5041126 *||14 Sep 1988||20 Aug 1991||Cook Incorporated||Endovascular stent and delivery system|
|US5059211 *||25 Jun 1987||22 Oct 1991||Duke University||Absorbable vascular stent|
|US5100429 *||20 Oct 1989||31 Mar 1992||C. R. Bard, Inc.||Endovascular stent and delivery system|
|US5102417 *||28 Mar 1988||7 Apr 1992||Expandable Grafts Partnership||Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft|
|US5104404 *||20 Jun 1991||14 Apr 1992||Medtronic, Inc.||Articulated stent|
|US5108416 *||13 Feb 1990||28 Apr 1992||C. R. Bard, Inc.||Stent introducer system|
|US5129910 *||26 Jul 1991||14 Jul 1992||The Regents Of The University Of California||Stone expulsion stent|
|US5133732 *||22 Mar 1989||28 Jul 1992||Medtronic, Inc.||Intravascular stent|
|US5135536 *||5 Feb 1991||4 Aug 1992||Cordis Corporation||Endovascular stent and method|
|US5147385 *||25 Oct 1990||15 Sep 1992||Schneider (Europe) A.G.||Stent and catheter for the introduction of the stent|
|US5158548 *||24 Jul 1991||27 Oct 1992||Advanced Cardiovascular Systems, Inc.||Method and system for stent delivery|
|US5161547 *||28 Nov 1990||10 Nov 1992||Numed, Inc.||Method of forming an intravascular radially expandable stent|
|US5192307 *||5 Feb 1992||9 Mar 1993||Wall W Henry||Angioplasty stent|
|US5354309 *||13 Oct 1992||11 Oct 1994||Angiomed Ag||Apparatus for widening a stenosis in a body cavity|
|US5370691 *||26 Jan 1993||6 Dec 1994||Target Therapeutics, Inc.||Intravascular inflatable stent|
|US5383926 *||23 Nov 1992||24 Jan 1995||Children's Medical Center Corporation||Re-expandable endoprosthesis|
|US5423849 *||15 Jan 1993||13 Jun 1995||Target Therapeutics, Inc.||Vasoocclusion device containing radiopaque fibers|
|US5441515 *||23 Apr 1993||15 Aug 1995||Advanced Cardiovascular Systems, Inc.||Ratcheting stent|
|US5599291 *||4 Jan 1993||4 Feb 1997||Menlo Care, Inc.||Softening expanding ureteral stent|
|US5632771 *||25 Jan 1995||27 May 1997||Cook Incorporated||Flexible stent having a pattern formed from a sheet of material|
|US6146358 *||7 Apr 1992||14 Nov 2000||Cordis Corporation||Method and apparatus for delivery of therapeutic agent|
|US6974475||8 Dec 1987||13 Dec 2005||Wall W Henry||Angioplasty stent|
|EP0274846A1 *||1 Dec 1987||20 Jul 1988||Boston Scientific Corporation||Apparatus for treating hypertrophy of the prostate gland|
|EP0364787A1 *||29 Sep 1989||25 Apr 1990||EXPANDABLE GRAFTS PARTNERSHIP a Texas General Partnership||Expandable intraluminal graft|
|EP0481365A1 *||11 Oct 1991||22 Apr 1992||Angiomed Ag||Device for expanding a stenosis in a body duct|
|EP0540290A2 *||27 Oct 1992||5 May 1993||Advanced Cardiovascular Systems, Inc.||Expandable stents and method for making same|
|FR2617721A1 *||Title not available|
|FR2660562A1 *||Title not available|
|SU660689A1 *||Title not available|
|WO1983000997A1 *||15 Sep 1982||31 Mar 1983||WALLSTÉN, Hans, Ivar||Device for application in blood vessels or other difficultly accessible locations|
|WO1993006792A1 *||2 Oct 1992||15 Apr 1993||Scimed Life Systems, Inc.||Biodegradable drug delivery vascular stent|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US8545548||30 Mar 2007||1 Oct 2013||DePuy Synthes Products, LLC||Radiopaque markers for implantable stents and methods for manufacturing the same|
|US9233015||14 Mar 2013||12 Jan 2016||Trivascular, Inc.||Endovascular delivery system with an improved radiopaque marker scheme|
|US9693885||11 Jan 2013||4 Jul 2017||DePuy Synthes Products, Inc.||Radiopaque markers for implantable stents and methods for manufacturing the same|
|U.S. Classification||623/1.15, 623/1.34|
|International Classification||A61F2/00, A61F2/88, A61F2/92|
|Cooperative Classification||A61F2250/0098, A61F2240/001, A61F2/885, A61F2/92, A61F2/958|
|European Classification||A61F2/92, A61F2/88B|
|13 Sep 2010||AS||Assignment|
Free format text: CHANGE OF NAME;ASSIGNOR:ROBERTS, KIMBERLY D.;REEL/FRAME:024973/0553
Effective date: 20100910
Owner name: COOK INCORPORATED, INDIANA
|21 Jun 2011||CC||Certificate of correction|
|20 Sep 2011||CC||Certificate of correction|
|26 Nov 2013||FPAY||Fee payment|
Year of fee payment: 12