|Publication number||US20050123702 A1|
|Application number||US 10/954,886|
|Publication date||Jun 9, 2005|
|Filing date||Sep 30, 2004|
|Priority date||Dec 3, 2003|
|Also published as||US8323242, US20100179581|
|Publication number||10954886, 954886, US 2005/0123702 A1, US 2005/123702 A1, US 20050123702 A1, US 20050123702A1, US 2005123702 A1, US 2005123702A1, US-A1-20050123702, US-A1-2005123702, US2005/0123702A1, US2005/123702A1, US20050123702 A1, US20050123702A1, US2005123702 A1, US2005123702A1|
|Original Assignee||Jim Beckham|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (68), Referenced by (33), Classifications (10), Legal Events (2)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application is a continuation of U.S. patent application Ser. No. 10/726,960, filed Dec. 3, 2003 and U.S. patent application Ser. No. 10/726,464, filed Dec. 3, 2003.
This application is related to U.S. Pat. No. 6,746,425, issued Jun. 8, 2004, which is a continuation-in-part of U.S. patent application Ser. No. 08,873,413, filed Jun. 12, 1997, which claims benefit of U.S. provisional application 60/019,931, filed Jun. 14, 1996.
This invention relates to the field of balloons that are useful in angioplasty and other medical uses.
Catheters having inflatable balloon attachments have been used for reaching small areas of the body for medical treatments, such as in coronary angioplasty and the like. Balloons are exposed to large amounts of pressure. Additionally, the profile of balloons must be small in order to be introduced into blood vessels and other small areas of the body. Therefore, materials with high strength relative to film thickness are chosen. An example of these materials is PET (polyethylene terephthalate), which is useful for providing a non-compliant, high-pressure device. Unfortunately, PET and other materials with high strength-to-film thickness ratios tend to be scratch- and puncture-sensitive. Polymers that tend to be less sensitive, such as polyethylene, nylon and urethane are compliant and, at the same film thickness as the non-compliant PET, do not provide the strength required to withstand the pressure used for transit in a blood vessel and expansion to open an occluded vessel. Non-compliance, or the ability not to expand beyond a predetermined size on pressure and to maintain substantially a profile, is a desired characteristic for balloons so as not to rupture or dissect the vessel as the balloon expands. Further difficulties often arise in guiding a balloon catheter into a desired location in a patient due to the friction between the apparatus and the vessel through which the apparatus passes. The result of this friction is failure of the balloon due to abrasion and puncture during handling and use and also from over-inflation.
The present invention is directed to a non-compliant medical balloon suitable for angioplasty and other medical procedures and which integrally includes very thin inelastic fibers having high tensile strength, and methods for manufacturing the balloon. The fiber reinforced balloons of the present invention meet the requirements of medical balloons by providing superior burst strength; superior abrasion-, cut- and puncture-resistence; and superior structural integrity.
More particularly, the invention is directed to a fiber-reinforced medical balloon having a long axis, wherein the balloon comprises an inner polymeric wall capable of sustaining pressure when inflated or expanded and a fiber/polymeric matrix outer wall surrounding and reinforcing the inner polymeric wall. The fiber/polymeric matrix outer wall is formed from at least two layers of fibers and a polymer layer. The fibers of the first fiber layer are substantially equal in length to the length of the long axis of the balloon and run along the length of the long axis. But “substantially equal in length” is meant that the fiber is at least 75% as long as the length of the long axis of the balloon, and preferably is at least 90% as long. The fiber of the second fiber layer runs radially around the circumference of the long axis of the balloon substantially over the entire length of the long axis. By “substantially over the entire length” is meant that the fiber runs along at least the center 75% of the length of the long axis of the balloon, and preferably runs along at least 90% of the length. The fiber of the second fiber layer is substantially perpendicular to the fibers of the first fiber layer. By “substantially perpendicular to” is meant that the fiber of the second fiber layer can be up to about 10 degrees from the perpendicular.
The invention is further directed to processes for manufacturing a non-compliant medical balloon. In one embodiment, a thin layer of a polymeric solution is applied onto a mandrel, the mandrel having the shape of a medical balloon and being removable from the finished product. High-strength inelastic fibers are applied to the thin layer of polymer with a first fiber layer having fibers running substantially along the length of he long axis of the balloon and a second fiber layer having fiber running radially around the circumference of the long axis substantially over the entire length of the long axis. The fibers are then coated with a thin layer of a polymeric solution to form a fiber/polymeric matrix. The polymers are cured and the mandrel is removed to give the fiber-reinforced medical balloon.
In another embodiment of the invention, a polymer balloon is inflated and is maintained in its inflated state, keeping the shape of the balloon. High-strength inelastic fibers are applied to the surface of the balloon, with a first fiber layer having fibers running substantially along the length of the long axis of the balloon and a second fiber layer having fiber running radially around the circumference of the long axis substantially over the entire length of the long axis. The fibers are then coated with a thin layer of a polymeric solution to form a fiber/polymeric matrix. The fiber/polymeric matrix is cured to give the fiber-reinforced medical balloon, which can then be deflated for convenience, until use.
In a presently preferred embodiment, a thin coating of an adhesive is applied to the inflated polymer balloon or to the polymer-coated mandrel prior to applying the inelastic fibers.
Referring now to the drawings, wherein like reference numbers are used to designate like elements throughout the various views, several embodiments of the present invention are further described. The figures are not necessarily drawn to scale, and in some instances the drawings have been exaggerated or simplified for illustrative purposes only. One of ordinary skill in the art will appreciate the many possible applications and variations of the present invention based on the following examples of possible embodiments of the present invention.
A medical balloon in accordance with the present invention in one embodiment begins with an inflated polymeric balloon 2, as shown in
An alternate method of applying the longitudinal fibers involves first creating a fabric of longitudinal fibers by pulling taut multiple parallel fibers on a flat plate and coating with a polymeric solution to create a fabric. The fabric is then cut into a pattern such that it can be wrapped around the base balloon or mandrel.
Next, a second application of inelastic fiber 6 is applied to the circumference of the balloon, as shown in
After the hoop wind is completed, the exterior of the fiber-wound inflated balloon is coated with a polymeric solution and cured to form a composite, con-complaint fiber-reinforced medical balloon. The outer polymeric coating of the fiber/polymeric matrix secures and bonds the fibers to the underlying inflated balloon so that movement of the fibers is restricted during deflation of the composite balloon and subsequent inflation and deflation during use of the balloon. The polymeric solution can be applied several times, if desired. The polymeric solution can use the same polymer as or a polymer different from the polymer of the inflated polymeric balloon 2. The polymers should be compatible so that separation of the composite balloon is prevented or minimized.
In a second method of making a medical balloon of the present invention, a removable mandrel having the shape that is identical to the shape of the inside of the desired balloon is used. A shape such as shown in
In view of the high strength of the balloons of the present invention, it is possible to make balloons having a wall thickness less than conventional or prior art balloons without sacrifice of burst strength, abrasion resistance, or puncture resistance. The balloon wall thickness can be less than the thickness given in the examples hereinbelow.
In addition, the fiber-reinforced balloons of the present invention are non-compliant. That is, they are characterized by minimal axial stretch and minimal radial distention and by the ability not to expand beyond a predetermined size on pressure and to maintain substantially a profile.
Polymers and copolymers that can be used for the base balloon and/or the covering layer of the fiber/polymeric matrix include the conventional polymers and copolymers used in medical balloon construction, such as, but not limited to, polyethylene, polyethylene terephthalate (PET), polycaprolactam, polyesters, polyethers, polyamides, polyurethanes, polyimides, ABS copolymers, polyester/polyether block copolymers, ionomer resins, liquid crystal polymers, and rigid rod polymers.
The high-strength fibers are chosen to be inelastic. By “inelastic,” as used herein and in the appended claims, is meant that the fibers have very minimal elasticity or stretch. Zero elasticity or stretch is probably unobtainable taking into account the sensitivity of modem precision test and measurement instruments, affordable costs and other factors. Therefore, the term “inelastic” should be understood to mean fibers that are generally classified as inelastic but which, nevertheless, may have a detectable, but minimal elasticity or stretch. High strength inelastic fibers useful in the present invention include but are not limited to, Kevlar, Vectran, Spectra, Dacron, Dyneema, Terlon (PBT), Zylon (PBO), Polyimide (PIM), ultra high molecular weight polyethylene, and the like. In a presently preferred embodiment, the fibers are ribbon-like; that is, they have a flattened to a rectangular shape. The fibers of the first fiber layer may be the same as or different from the fiber of the second fiber layer.
The most advantageous density of the fiber wind is determinable through routine experimentation by one of ordinary skill in the art given the examples and guidelines herein. With respect to the longitudinally-placed fibers (along the long axis of the balloon) of the first fiber layer, generally about 15 to 30 fibers having a fiber thickness of about 0.0005 to 0.001 inch and placed equidistant from one another will provide adequate strength for a standard-sized medical balloon. With respect to the fiber of the hoop wind, or second fiber layer, fiber having a thickness of about 0.0005 to 0.001 inch and a wind density within the range of about 50 to 80 wraps per inch is generally adequate. The fiber of the second fiber layer is preferably continuous and is, for a standard-sized medical balloon, about 75-100 inches long.
The longitudinally placed fibers should be generally parallel to or substantially parallel to the long axis of the balloon for maximum longitudinal stability (non-stretch) of the balloon. The fibers of the hoop wind should be perpendicular to or substantially perpendicular to the fibers placed longitudinally for maximum radial stability (non-stretch) of the balloon. This distributes the force on the balloon surface equally and creates “pixels” of equal shape and size. In the case where the fibers of the hoop wind are at a small acute angle (e.g. about 10 degrees or more) to the longitudinal fibers, two hoop winds (in opposite directions) can be used for minimizing radial distension.
The following examples are provided to illustrate the practice of the present invention, and are intended neither to define nor to limit the scope of the invention in any manner.
An angioplasty balloon, as shown in
Kevlar® fibers are placed, by hand, along the length of the balloon as shown in
Next, a hoop wind of Kevlar® fiber is applied radially around the circumference of and over substantially the entire length of the long axis of the balloon, as shown in
The fiber-wound based PET balloon is then coated with a 10% solution of Texin® 5265 polyurethane in dimethylacetamide (DMA) and allowed to cure at room temperature. Five additional coating of the polurethane solution are applied in about 6-hour increments, after which the pressure in the balloon is released. The resulting composite fiber-reinforced balloon is non-compliant and exhibits superior burst strength and abrasion and puncture resistance.
3M-75 is a tacky adhesive available from the 3M Company, Minneapolis, Minn. Kevlar® is a high strength, inelastic fiber available from the DuPont Company, Wilmington Del. Texin® 5265 is a polyurethane polymer available from Miles, Inc., Pittsburgh, Pa.
The procedure of Example 1 was repeated with the exception that Vectran® fiber, having a thickness of 0.0005 inch is used in place of the Kevlar® fiber. The resulting composite balloon is axially and radially non-compliant at very high working pressures. The balloon has very high tensile strength and abrasion and puncture resistance.
Vectran® is a high strength fiber available from Hoechst-Celanese, Charlotte, N.C.
A mandrel in the shape of a balloon as shown in
The procedure of Example 3 is repeated using high strength Spectra® fiber in place of Vectran® fiber. Spectra® fiber is available from Allied Signal, Inc., Morristown, N.J.
The procedure of Example 1 is repeated using Ultra High Molecular Weight Polyethylene (Spectra 2000) fiber, which has been flattened on a roll mill. To the flattened fiber is applied a thin coat of a solution of 1-MP Tecoflex® adhesive in a 60-40 solution of methylene chloride and methylethylketone. The fiber is applied to the balloon as in Example 1 using 30 longitudinal fibers, each substantially equal in length to the length of the long axis of the balloon, and a hoop wind of 54 wraps per inch. The fibers are then coated with the Tecoflex® solution.
Tecoflex® is supplied by Thermedics Inc., Woburn, Mass.
A balloon-shaped solid mandrel made of a low melting temperature metal alloy is coated with a thin layer of Texin® 5265/DMA solution (10%). Vectran® fibers are applied as in Example 1, followed by coating with Texin®/DMA. The metal mandrel is melted out using hot water. A very high strength, abrasion-resistant, composite balloon is obtained, which is non-compliant.
Following the procedures of Example 6, a mandrel is coated with a very thin layer of PIM polyimide (2,2-dimethylbenzidine) in solution in cyclopentanone. Polyimide fibers are applied, and the composite balloon is then completed with additional applications of the PIM solution. The mandrel is removed to give a high strength, puncture-resistant balloon having an extremely cohesive fiber/matrix composite wall that is resistant to delarnination.
A balloon is constructed as in Example 7, except that the longitudinal fibers are replaced by a longitudinally oriented thin film made of polyimide LARC-IA film (available from IMITEC, Schenectady, N.Y.). The film is cut into a mandrel-shaped pattern and applied to the mandrel, over which the polyimide hoop fibers and the PIM solution are applied.
Although the illustrative embodiment has been described in detail, it should be understood that various changes, substitutions and alterations can be made therein without departing from the spirit and scope of the invention as defined by the appended claims.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US4572186 *||Dec 7, 1983||Feb 25, 1986||Cordis Corporation||Vessel dilation|
|US4637396 *||Oct 26, 1984||Jan 20, 1987||Cook, Incorporated||Balloon catheter|
|US4702252 *||Jan 27, 1986||Oct 27, 1987||Smiths Industries Public Limited Company||Catheters|
|US4706670 *||Nov 26, 1985||Nov 17, 1987||Meadox Surgimed A/S||Dilatation catheter|
|US4796629 *||Jun 3, 1987||Jan 10, 1989||Joseph Grayzel||Stiffened dilation balloon catheter device|
|US5066285 *||Jan 26, 1990||Nov 19, 1991||Cordis Corporation||Catheter introducer sheath made of expanded polytetrafluoroethylene|
|US5078727 *||Jun 22, 1990||Jan 7, 1992||Hannam Peter H||Catheters|
|US5108415 *||Dec 19, 1989||Apr 28, 1992||Cordis Corporation||Balloons for medical devices and fabrication thereof|
|US5112304 *||Mar 17, 1989||May 12, 1992||Angeion Corporation||Balloon catheter|
|US5116360 *||Dec 27, 1990||May 26, 1992||Corvita Corporation||Mesh composite graft|
|US5171297 *||Apr 21, 1992||Dec 15, 1992||Angeion Corporation||Balloon catheter|
|US5201706 *||Mar 11, 1991||Apr 13, 1993||Toray Industries, Inc.||Catheter with a balloon reinforced with composite yarn|
|US5264260 *||Jun 20, 1991||Nov 23, 1993||Saab Mark A||Dilatation balloon fabricated from low molecular weight polymers|
|US5270086 *||Jul 9, 1991||Dec 14, 1993||Schneider (Usa) Inc.||Multilayer extrusion of angioplasty balloons|
|US5290306 *||Nov 29, 1989||Mar 1, 1994||Cordis Corporation||Puncture resistant balloon catheter|
|US5295960 *||Apr 1, 1992||Mar 22, 1994||Applied Medical Resources Corporation||Catheter with interior balloon|
|US5314443 *||Jan 21, 1993||May 24, 1994||Meadox Medicals, Inc.||Prostate balloon dilatation catheter|
|US5330429 *||Jan 8, 1993||Jul 19, 1994||Toray Industries, Inc.||Catheter with a balloon reinforced with composite yarn|
|US5338299 *||Sep 29, 1992||Aug 16, 1994||Angeion Corporation||Balloon catheter|
|US5344401 *||May 12, 1993||Sep 6, 1994||Interventional Technologies Inc.||Catheter balloon formed from a polymeric composite|
|US5358485 *||Aug 16, 1993||Oct 25, 1994||Schneider (Usa) Inc.||Cutter for atherectomy catheter|
|US5451209 *||Feb 16, 1994||Sep 19, 1995||Advanced Cardiovascular Systems, Inc.||Intraluminal catheter with a composite shaft|
|US5453076 *||Apr 15, 1993||Sep 26, 1995||Kiyota; Yoshiharu||Internal cardiac assist apparatus|
|US5470314 *||Jul 22, 1994||Nov 28, 1995||Walinsky; Paul||Perfusion balloon catheter with differential compliance|
|US5478320 *||Jan 31, 1994||Dec 26, 1995||Cordis Corporation||Puncture resistant balloon catheter and method of manufacturing|
|US5492532 *||Aug 15, 1994||Feb 20, 1996||B. Braun Medical, Inc.||Balloon catheter|
|US5549552 *||Mar 2, 1995||Aug 27, 1996||Scimed Life Systems, Inc.||Balloon dilation catheter with improved pushability, trackability and crossability|
|US5587125 *||Aug 15, 1994||Dec 24, 1996||Schneider (Usa) Inc.||Non-coextrusion method of making multi-layer angioplasty balloons|
|US5647848 *||Jun 7, 1995||Jul 15, 1997||Meadox Medicals, Inc.||High strength low compliance composite balloon for balloon catheters|
|US5755690 *||Oct 21, 1994||May 26, 1998||C. R. Bard||Multiple layer high strength balloon for dilatation catheter|
|US5759172 *||Apr 9, 1996||Jun 2, 1998||Cordis Corporation||Balloon catheter with lobed balloon and method for manufacturing such a catheter|
|US5769817 *||Feb 28, 1997||Jun 23, 1998||Schneider (Usa) Inc.||Coextruded balloon and method of making same|
|US5772681 *||Mar 2, 1994||Jun 30, 1998||Metra Aps||Dilation catheter|
|US5788979 *||Feb 10, 1997||Aug 4, 1998||Inflow Dynamics Inc.||Biodegradable coating with inhibitory properties for application to biocompatible materials|
|US5820613 *||Jan 31, 1996||Oct 13, 1998||Cordis Corporation||Balloon catheter with reinforced and elastically deformable basic body|
|US5868779 *||Aug 15, 1997||Feb 9, 1999||Ruiz; Carlos E.||Apparatus and methods for dilating vessels and hollow-body organs|
|US5928181 *||Nov 21, 1997||Jul 27, 1999||Advanced International Technologies, Inc.||Cardiac bypass catheter system and method of use|
|US5972441 *||Feb 24, 1997||Oct 26, 1999||W. L. Gore & Associates, Inc.||Thin-wall polytetrafluoroethylene tube|
|US6007544 *||Apr 16, 1998||Dec 28, 1999||Beth Israel Deaconess Medical Center||Catheter apparatus having an improved shape-memory alloy cuff and inflatable on-demand balloon for creating a bypass graft in-vivo|
|US6012457 *||Jul 8, 1997||Jan 11, 2000||The Regents Of The University Of California||Device and method for forming a circumferential conduction block in a pulmonary vein|
|US6024722 *||Dec 27, 1994||Feb 15, 2000||Scimed Life Systems, Inc.||Thermoplastic polyimide balloon catheter construction|
|US6024740 *||Jul 8, 1997||Feb 15, 2000||The Regents Of The University Of California||Circumferential ablation device assembly|
|US6027779 *||May 24, 1994||Feb 22, 2000||W. L. Gore & Associates, Inc.||Thin-wall polytetrafluoroethylene tube|
|US6036697 *||Jul 9, 1998||Mar 14, 2000||Scimed Life Systems, Inc.||Balloon catheter with balloon inflation at distal end of balloon|
|US6085705 *||Dec 11, 1998||Jul 11, 2000||Diesel Engine Retarders, Inc.||Variable lost motion valve actuator and method|
|US6117101 *||Nov 25, 1998||Sep 12, 2000||The Regents Of The University Of California||Circumferential ablation device assembly|
|US6124007 *||Mar 6, 1996||Sep 26, 2000||Scimed Life Systems Inc||Laminate catheter balloons with additive burst strength and methods for preparation of same|
|US6127597 *||Mar 6, 1998||Oct 3, 2000||Discotech N.V.||Systems for percutaneous bone and spinal stabilization, fixation and repair|
|US6156254 *||Feb 1, 1999||Dec 5, 2000||Ranier Limited||Method of manufacturing a balloon member for a balloon catheter|
|US6164283 *||Jan 29, 1999||Dec 26, 2000||The Regents Of The University Of California||Device and method for forming a circumferential conduction block in a pulmonary vein|
|US6183492 *||Aug 27, 1998||Feb 6, 2001||Charles C. Hart||Perfusion-isolation catheter apparatus and method|
|US6187013 *||Jun 6, 1995||Feb 13, 2001||Meadox Medicals, Inc.||Catheter with stent and method for the production of a catheter with stent|
|US6234995 *||Nov 12, 1998||May 22, 2001||Advanced Interventional Technologies, Inc.||Apparatus and method for selectively isolating a proximal anastomosis site from blood in an aorta|
|US6245064 *||Jan 11, 2000||Jun 12, 2001||Atrionix, Inc.||Circumferential ablation device assembly|
|US6254599 *||Mar 22, 1999||Jul 3, 2001||Atrionix, Inc.||Circumferential ablation device assembly|
|US6263236 *||Nov 29, 1999||Jul 17, 2001||Illumenex Corporation||Non-occlusive expandable catheter|
|US6270902 *||Apr 23, 1997||Aug 7, 2001||C. R. Bard, Inc.||Method of improving the adherence of certain crosslinked polymer coatings containing PEO or PVP to a substrate|
|US6290485 *||Sep 15, 1999||Sep 18, 2001||Lixiao Wang||Mold for forming a balloon catheter having stepped compliance curve|
|US6293237 *||Jun 16, 2000||Sep 25, 2001||Diesel Engine Retarders, Inc.||Variable lost motion valve actuator and method|
|US6305378 *||Aug 27, 1999||Oct 23, 2001||The Regents Of The University Of California||Device and method for forming a circumferential conduction block in a pulmonary vein|
|US6315751 *||Aug 15, 1997||Nov 13, 2001||Cleveland Clinic Foundation||Cardiopulmonary bypass system using vacuum assisted venous drainage|
|US6328925 *||Sep 26, 2000||Dec 11, 2001||Scimed Life Systems, Inc.||Laminate catheter balloons with additive burst strength and methods for preparation of same|
|US6474277 *||Sep 15, 2000||Nov 5, 2002||Diesel Engine Retarders, Inc.||Method and apparatus for valve seating velocity control|
|US6510824 *||Dec 29, 2000||Jan 28, 2003||Diesel Engine Retarders, Inc.||Variable lost motion valve actuator and method|
|US6550433 *||Jun 24, 2002||Apr 22, 2003||Diesel Engine Retarders, Inc.||Engine valve actuator with valve seating control|
|US6647723 *||Aug 20, 2002||Nov 18, 2003||International Engine Intellectual Property Company, Llc||Control strategy for counteracting incipient turbocharger surging using a variable valve actuation mechanism for through-cylinder bleed|
|US6655349 *||Dec 30, 2002||Dec 2, 2003||Caterpillar Inc||System for controlling a variable valve actuation system|
|US20030221663 *||Apr 8, 2003||Dec 4, 2003||Vanderpoel Richard E.||Compact lost motion system for variable valve actuation|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7273471 *||Dec 23, 2003||Sep 25, 2007||Advanced Cardiovascular Systems, Inc.||Catheter balloon having a porous layer with ridges|
|US7309324 *||Oct 15, 2004||Dec 18, 2007||Futuremed Interventional, Inc.||Non-compliant medical balloon having an integral woven fabric layer|
|US7354419||Oct 15, 2004||Apr 8, 2008||Futuremed Interventional, Inc.||Medical balloon having strengthening rods|
|US7682335 *||Oct 15, 2004||Mar 23, 2010||Futurematrix Interventional, Inc.||Non-compliant medical balloon having an integral non-woven fabric layer|
|US7780629||May 21, 2007||Aug 24, 2010||Futurematrix Interventional, Inc.||Non-compliant medical balloon having an integral non-woven fabric layer|
|US7914487||Mar 23, 2007||Mar 29, 2011||Futurematrix Interventional, Inc.||Non-compliant medical balloon having braided or knitted reinforcement|
|US7943221||May 22, 2006||May 17, 2011||Boston Scientific Scimed, Inc.||Hinged compliance fiber braid balloon|
|US7985235||Mar 6, 2009||Jul 26, 2011||Bard Peripheral Vascular, Inc.||Balloon dilation catheter having transition from coaxial lumens to non-coaxial multiple lumens|
|US7985236||Jun 9, 2009||Jul 26, 2011||Bard Peripheral Vascular, Inc.||Rapid exchange balloon dilation catheter having reinforced multi-lumen distal portion|
|US8002741||May 21, 2007||Aug 23, 2011||Bard Peripheral Vascular, Inc.||Non-compliant medical balloon having an integral woven fabric layer|
|US8002744||Aug 6, 2008||Aug 23, 2011||Bard Peripheral Vascular, Inc||Non-compliant medical balloon|
|US8105275||Aug 24, 2010||Jan 31, 2012||Bard Peripheral Vascular, Inc.||Non-compliant medical balloon having an integral non-woven fabric layer|
|US8221351||Jan 29, 2010||Jul 17, 2012||Bard Peripheral Vascular, Inc.||Non-compliant medical balloon having an integral non-woven fabric layer|
|US8236221||Aug 7, 2009||Aug 7, 2012||Bard Peripheral Vascular, Inc.||Non-compliant medical balloon|
|US8313601||Aug 7, 2009||Nov 20, 2012||Bard Peripheral Vascular, Inc.||Non-compliant medical balloon|
|US8349237||Sep 28, 2011||Jan 8, 2013||Boston Scientific Scimed, Inc.||High pressure balloon|
|US8353868||Jan 15, 2013||Bard Peripheral Vascular, Inc.||Medical balloon having strengthening rods|
|US8597240||Feb 2, 2012||Dec 3, 2013||Futurematrix Interventional, Inc.||Coaxial catheter shaft having balloon attachment feature with axial fluid path|
|US8697212||Jan 7, 2013||Apr 15, 2014||Boston Scientific Scimed, Inc.||High pressure balloon|
|US8708955||Jun 2, 2009||Apr 29, 2014||Loma Vista Medical, Inc.||Inflatable medical devices|
|US8728110||Jan 16, 2009||May 20, 2014||Bard Peripheral Vascular, Inc.||Balloon dilation catheter shaft having end transition|
|US8814899||Feb 23, 2009||Aug 26, 2014||Futurematrix Interventional, Inc.||Balloon catheter pressure relief valve|
|US8858855||Apr 20, 2006||Oct 14, 2014||Boston Scientific Scimed, Inc.||High pressure balloon|
|US8979886||Aug 7, 2006||Mar 17, 2015||W. L. Gore & Associates, Inc.||Medical balloon and method of making the same|
|US9126022||Aug 16, 2010||Sep 8, 2015||Cook Medical Technologies Llc||Textile-reinforced high-pressure balloon|
|US20060085022 *||Oct 15, 2004||Apr 20, 2006||Kelli Hayes||Non-compliant medical balloon having an integral woven fabric layer|
|US20060085023 *||Oct 15, 2004||Apr 20, 2006||Davies William F Jr||Medical balloon having strengthening rods|
|US20060085024 *||Oct 15, 2004||Apr 20, 2006||Pepper Lanny R||Non-compliant medical balloon having an integral non-woven fabric layer|
|US20070016133 *||Jul 5, 2005||Jan 18, 2007||Futurematrix Interventional, Inc.||Rapid exchange balloon dilation catheter having reinforced multi-lumen distal portion|
|EP2700428A1 *||Jul 27, 2007||Feb 26, 2014||Gore Enterprise Holdings, Inc.||Medical balloon and method of making the same|
|WO2008020980A1 *||Jul 27, 2007||Feb 21, 2008||Gore Enterprise Holdings Inc||Medical balloon and method of making the same|
|WO2008063782A2 *||Oct 12, 2007||May 29, 2008||Bard Inc C R||Inflatable structure with braided layer|
|WO2011028397A1 *||Aug 16, 2010||Mar 10, 2011||Cook Incorporated||Textile-reinforced high-pressure balloon|
|U.S. Classification||428/36.3, 606/192, 604/103.06|
|Cooperative Classification||A61M2025/1086, Y10T156/1062, Y10T428/1369, A61M25/104, Y10T156/1075|
|Sep 30, 2004||AS||Assignment|
Owner name: FUTUREMED INTERVENTIONAL, INC., TEXAS
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:BECKHAM, JIM;REEL/FRAME:015858/0498
Effective date: 20040928
|Oct 28, 2009||AS||Assignment|
Owner name: C.R. BARD, INC., ARIZONA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:FUTUREMED INTERVENTIONAL, INC.;REEL/FRAME:023439/0992
Effective date: 20040722