USRE32983E - Balloon and manufacture thereof - Google Patents
Balloon and manufacture thereof Download PDFInfo
- Publication number
- USRE32983E USRE32983E US06/914,108 US91410886A USRE32983E US RE32983 E USRE32983 E US RE32983E US 91410886 A US91410886 A US 91410886A US RE32983 E USRE32983 E US RE32983E
- Authority
- US
- United States
- Prior art keywords
- tubing
- balloon
- psi
- mpa
- temperature
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/10—Balloon catheters
- A61M25/1027—Making of balloon catheters
- A61M25/1029—Production methods of the balloon members, e.g. blow-moulding, extruding, deposition or by wrapping a plurality of layers of balloon material around a mandril
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T428/00—Stock material or miscellaneous articles
- Y10T428/13—Hollow or container type article [e.g., tube, vase, etc.]
- Y10T428/1352—Polymer or resin containing [i.e., natural or synthetic]
- Y10T428/1397—Single layer [continuous layer]
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T428/00—Stock material or miscellaneous articles
- Y10T428/31504—Composite [nonstructural laminate]
- Y10T428/31786—Of polyester [e.g., alkyd, etc.]
Definitions
- This invention relates to balloon catheters which are especially useful in medical dilation procedures.
- Gruntzig et al. disclose an improved technique for the use of a dilating catheter to relieve arterial stenosis. According to Gruntzig et al. the technique of transluminal angioplasty for the treatment of atherosclerotic obstruction of the femoral artery was first introduced in 1964 by Dotter and Judkins.
- Balloon catheters are not limited in their use to the relief of arterial stenosis but have been found useful in many medical applications involving not only insertion into blood vessels but also involving insertion into a variety of body cavities.
- Balloons can be made from a variety of known materials which are generally of the thermoplastic polymeric type.
- ethylene-butylene-styrene block copolymers admixed with low molecular weight polystyrene and, optionally, polypropylene, and similar compositions employing butadiene or isoprene in place of the ethylene and butylene; poly(vinyl chloride); polyurethanes; copolyesters; thermoplastic rubbers; siliconepolycarbonate copolymers; and ethylene-vinyl acetate copolymers.
- a further object is to provide balloons which, because of their superior physical properties, have thinner wall thickness than commonly used balloons.
- Another object is to provide such balloons which, because of their flexibility and thin walls, are more readily collapsible and more easily transportable in the body.
- a further object is to provide such balloons which, if they burst under pressure, burst in the axial direction to give an axial rupture, thus ensuring atraumatic removal, it being well known that a balloon which bursts in a circumferential direction may provide fragments which either are removable only with difficulty or are not removable at all nonsurgically.
- a further object is to provide such balloons which, because of their superior physical properties, can be used in medical procedures with a greater probability of success.
- Another object is to provide such balloons which, because of their superior physical properties, can be used in medical procedures under conditions not currently achievable using commonly available balloons. Still another object is to provide a process for fabricating such balloons.
- FIG. 1 is an elevation, in section, showing only the back half of the mold, balloon, tubing and attendant hardware of an apparatus which can be used to form the balloon of the invention from drawn polymeric tubing.
- FIG. 2 shows the radial expansion (%) and burst pressure (psi) of three balloons of the invention (C, D and E) as compared to the radial expansion (%) and burst pressure (psi) of two balloons of the art (A and B).
- the invention resides in an improved balloon having an unusual combination of physical properties and which is especially useful in medical dilation procedures.
- the invention also resides in a process for fabricating such balloons, and in a dilatation balloon catheter comprising such an improved balloon.
- the process comprises, at a temperature within the range extending from the second order transition temperature to the first order transition temperature, preferably at a temperature of 84°-99° C., more preferably 86°-96° C., drawing a polymeric, preferably a polyethylene terephthalate (PET) homopolyester, tubing, having a finite length (L 1 ) and an internal diameter (ID) which is preferably about one-half the outer diameter (OD), to a length (L 2 ) which is preferably 3 to 6 L 1 , and thereafter expanding the drawn tubing of internal diameter ID 1 and outer diameter OD 1 by expanding means to an internal diameter (ID 2 ) which is preferably 6 to 8 ID and an outer diameter (OD 2 ) which is preferably about 3 to about 4 OD, followed by cooling the drawn and expanded tubing to less than its second order transition temperature, the balloon thus formed having a burst pressure, that is, the internal pressure at which the balloon bursts, of at least 200 psi (1.4 MPa) and
- Such preferred tubing can be commonly formed by conventional extrusion techniques from PET homopolyester resin having an intrinsic viscocity of 1.0 to 1.3 and a density of 1.35 to 1.45.
- the balloon prepared by the process of this invention exhibits an unusual combination of film properties, such as toughness, flexibility and tensile strength.
- the balloon of the invention exhibits a burst pressure of at least 200 psi (1.4 MPa), preferably at least 400 psi (2.8 MPa), more preferably at least 500 psi (3.4 MPa) at ambient temperature (20° C.).
- the balloon of the invention exhibits a radial expansion beyond nominal inflated diameter of less than 5% when at a pressure of 200 psi (1.4 MPa) and less than 10% when at a pressure of 400 psi (2.8 MPa).
- FIG. 2 herein depicts burst pressure vs. radial expansion for two balloons (A and B) commonly available commercially and comprised of poly(vinyl chloride) and for three balloons (C, D and E) of the invention and comprised of PET homopolyester. Balloons A and C have nominal outer diameters of 3.7 mm; balloons B and D, 5.0 mm; and E, 6.0 mm.
- the wall thicknesses of A through E were, respectively, about 0.028, 0.038, 0.028, 0.038, and 0.045 mm.
- Radial expansion data for the balloons of the invention were calculated from the well known membrane equation and the ultimate elongation measured on flat film samples which were similarly biaxially oriented. Similar calculations were made for the poly(vinyl chloride) balloons except that published data were used for ultimate elongation. It can be seen that the burst pressures for the balloons of the invention are, respectively, 3.2, 3.4 and 3.5 times those for the balloons of the art.
- radial expansion is determined from the point at which the balloon is pressurized so as to be free of wrinkles, that is, after being inflated from its collapsed position to its nominal inflated diameter; a gas pressure of 75-100 psi (0.5-0.7 MPa) is required to reach this first expanded position with the PET homopolyester balloon of this invention.
- a balloon of higher strength can be produced from the polymeric tubing by operating at high stretch ratios, that is, at the upper ends of the draw and expansion ratios. The balloon thus produced exhibits lower elongation, which is reflected in lower expansion values at a given inflation pressure, vis-a-vis a balloon produced under lower stretch conditions.
- Intrinsic viscosity is determined herein by means of ANSI/ASTM D 2857-70 and density, by ASTM D 1505. Burst pressure is determined by a simple laboratory procedure whereby one end of the polymeric balloon is sealed off and a pressurized gas is introduced incrementally into the other end. The inflation pressure at which the balloon bursts at about 20° C. (ambient temperature) is referred to herein as the burst pressure.
- the process by which the balloon is prepared can be carried out in a conventional manner with conventional equipment using a specialized polymer as the material of fabrication.
- the tubing of appropriate dimensions and of high molecular weight polymer is first drawn at a suitable temperature from a length L 1 to a length L 2 .
- the drawn tubing is then expanded in a confining apparatus such as depicted in FIG. 1 which is a part of this specification.
- one end of the tubing can be filled with a fluid under pressure during the expansion step of the process.
- the mold has a cavity of dimensions commensurate with the desired size of the balloon to be produced.
- the open end of the tubing is equipped with a suitable fitting so that a pressurized fluid can be introduced into the tubing.
- Any suitable fluid can be used to pressurize for inflation of drawn tubing, for example, a gas, such as nitrogen. If the tubing extends beyond the mold, such as shown in FIG. 1, use of a restraining means is preferred to maintain the dimensions of the tubing in the region outside the mold while pressure is being applied to the inside wall of the tubing.
- the restraining means can be of any material which is nondeformable under the tubing expansion conditions. After the drawn tubing is positioned in the mold, heat is applied to raise the tubing temperature. Similar temperatures can be used for both the drawing and expanding steps.
- a suitable temperature is the range extending from the second order transition temperature to the first order transition temperature of the polymer from which the tubing has been fabricated.
- the preferred temperature is 84°-99° C., more preferably 86°-96° C.
- PET homopolymer is the only polymer demonstrated herein, it is to be understood that any high molecular weight polymer that can be extruded into tubing and then drawn and expanded in general accordance with the aforesaid process is operable, for example, a PET copolyester or even a nonpolyester polymer, provided the resultant balloon exhibits the desired film properties, such as toughness, flexibility and tensile strength. If the balloon is to be used in medical procedures involving contact with tissue, the polymeric material of construction should be tissue compatible.
- the intrinsic viscocity a measure of the molecular weight of the polymer, be high.
- the polymer is a homopolyester or copolyester PET resin, special, but well known, techniques may be employed to increase the molecular weight to the necessary level.
- the most commonly available PET homopolyester generally has an intrinsic viscosity of about 0.5 to 0.6, well below the requisite 1.0 to 1.3.
- tubing drawing step is performed prior to the tubing expansion step, the latter can be performed immediately after the drawing of the tubing, or it can be performed at a later time.
- drawing of the tubing can be performed using any suitable drawing means, it conveniently can be effected in the apparatus depicted in FIG. 1 so that the drawn tubing is already in place to perform the expansion. Because of the recovery characteristic of shaped polymeric structures which are drawn by the procedures used herein, it may be necessary to maintain axial tension on the drawn tubing during the expansion step. Consistent with all the above and readily understandable to one skilled in the art, the drawing and expansion steps can be performed at the same or at different temperatures. The desired temperature can be achieved by any suitable heat generating means. In actual experiments carried out herein with respect to the use of PET homopolyester, hot water was employed. Drawing of the tubing herein was achieved by using the weight of the mold.
- a dilatation balloon catheter comprising the balloon of the invention can be fabricated by means of conventional techniques, and such a catheter can be used in accordance with accepted medical procedures.
- Tubing (1.5 mm OD ⁇ 0.75 mm ID) is inserted into a mold having a cavity shaped in the form of a cylinder, similar to that shown in FIG. 1, with ends which taper to smaller diameter cylinder slightly larger than the tubing OD.
- the diameter D of the cavity is about 5 mm and its length A+B+C, about 15 mm.
- the tubing is pinched off at the lower end of the mold, and weights are attached to the mold to produce the required axial drawing about (3 ⁇ ).
- the total weight of mold and weights is about 150 g.
- the weight of the assembly (mold, tubing and weights) is supported by the tubing which is fixed at its upper end by insertion into a tubing fitting.
- the assembly is inserted into a liquid medium at 87° C. and allowed to heat for about 1 minute. During that time axial orientation occurs because of the weight of the assembly in the heated liquid supported by the tubing.
- About 200 psi (1.4 MPa) of gas pressure is applied to the tubing, which radially orients the tubing (about 3.33 ⁇ ) in the mold cavity. This pressurization step lasts about two minutes, during which there is some additional axial draw.
- the assembly is cooled by immersion into a cold liquid, the pressure is released and the finished balloon is removed from the mold.
- the process of this example was used to produce balloons having wall thicknesses of about 0.028-0.045 mm and burst strength of 480-525 psi (3.3-3.6 MPa), as showing in FIG. 2.
- the failure mode (on bursting) of such balloons is an elliptically shaped hole having its major axis substantially along the axial direction.
- An alternate fabrication method and one more suitable for mass production would utilize a stationary mold having internal flow passages for hot and cold fluids.
- the tubing would be axially oriented to predetermined ratios by a stepper motor rather than by means of an attached weight. During the radial expansion phase, additional axial drawing may be required.
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- Health & Medical Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Engineering & Computer Science (AREA)
- Life Sciences & Earth Sciences (AREA)
- Anesthesiology (AREA)
- Child & Adolescent Psychology (AREA)
- Biophysics (AREA)
- Pulmonology (AREA)
- Manufacturing & Machinery (AREA)
- Biomedical Technology (AREA)
- Hematology (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Media Introduction/Drainage Providing Device (AREA)
- Materials For Medical Uses (AREA)
Abstract
Description
Claims (14)
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US06/914,108 USRE32983E (en) | 1983-07-05 | 1986-10-01 | Balloon and manufacture thereof |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US06/510,812 US4490421A (en) | 1983-07-05 | 1983-07-05 | Balloon and manufacture thereof |
US06/914,108 USRE32983E (en) | 1983-07-05 | 1986-10-01 | Balloon and manufacture thereof |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US06/510,812 Reissue US4490421A (en) | 1983-07-05 | 1983-07-05 | Balloon and manufacture thereof |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US07/287,234 Division USRE33561E (en) | 1983-07-05 | 1988-12-21 | Balloon and manufacture thereof |
Publications (1)
Publication Number | Publication Date |
---|---|
USRE32983E true USRE32983E (en) | 1989-07-11 |
Family
ID=27057037
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US06/914,108 Expired - Lifetime USRE32983E (en) | 1983-07-05 | 1986-10-01 | Balloon and manufacture thereof |
Country Status (1)
Country | Link |
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US (1) | USRE32983E (en) |
Cited By (112)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5108415A (en) * | 1988-10-04 | 1992-04-28 | Cordis Corporation | Balloons for medical devices and fabrication thereof |
US5163989A (en) * | 1990-08-27 | 1992-11-17 | Advanced Cardiovascular Systems, Inc. | Method for forming a balloon mold and the use of such mold |
US5236659A (en) * | 1988-10-04 | 1993-08-17 | Cordis Corporation | Tailoring expansion properties of balloons for medical devices |
US5246421A (en) * | 1992-02-12 | 1993-09-21 | Saab Mark A | Method of treating obstructed regions of bodily passages |
US5264260A (en) * | 1991-06-20 | 1993-11-23 | Saab Mark A | Dilatation balloon fabricated from low molecular weight polymers |
US5304197A (en) * | 1988-10-04 | 1994-04-19 | Cordis Corporation | Balloons for medical devices and fabrication thereof |
US5320634A (en) * | 1990-07-03 | 1994-06-14 | Interventional Technologies, Inc. | Balloon catheter with seated cutting edges |
US5328468A (en) * | 1991-10-08 | 1994-07-12 | Terumo Kabushiki Kaisha | Balloon for blood vessel-dilating catheter |
US5330428A (en) * | 1991-05-14 | 1994-07-19 | Scimed Life Systems, Inc. | Dilatation catheter having a random copolymer balloon |
US5336234A (en) * | 1992-04-17 | 1994-08-09 | Interventional Technologies, Inc. | Method and apparatus for dilatation of a stenotic vessel |
US5335675A (en) * | 1988-11-15 | 1994-08-09 | Family Health International | Stress-softened elastomeric films, articles, and method and apparatus for making such films and articles |
US5337734A (en) * | 1992-10-29 | 1994-08-16 | Advanced Polymers, Incorporated | Disposable sheath with optically transparent window formed continuously integral therewith |
US5342386A (en) * | 1992-10-26 | 1994-08-30 | Cordis Corporation | Catheter with multiple flexibilities along the shaft |
US5342301A (en) * | 1992-08-13 | 1994-08-30 | Advanced Polymers Incorporated | Multi-lumen balloons and catheters made therewith |
US5348538A (en) * | 1992-09-29 | 1994-09-20 | Scimed Life Systems, Inc. | Shrinking balloon catheter having nonlinear or hybrid compliance curve |
US5356591A (en) * | 1988-10-04 | 1994-10-18 | Cordis Corporation | Tailoring expansion properties of balloons for medical devices |
US5383856A (en) * | 1993-03-19 | 1995-01-24 | Bersin; Robert M. | Helical spiral balloon catheter |
US5411477A (en) * | 1990-05-11 | 1995-05-02 | Saab; Mark A. | High-strength, thin-walled single piece catheters |
US5499973A (en) * | 1994-09-08 | 1996-03-19 | Saab; Mark A. | Variable stiffness balloon dilatation catheters |
US5500180A (en) * | 1992-09-30 | 1996-03-19 | C. R. Bard, Inc. | Method of making a distensible dilatation balloon using a block copolymer |
US5554120A (en) * | 1994-07-25 | 1996-09-10 | Advanced Cardiovascular Systems, Inc. | Polymer blends for use in making medical devices including catheters and balloons for dilatation catheters |
US5624392A (en) * | 1990-05-11 | 1997-04-29 | Saab; Mark A. | Heat transfer catheters and methods of making and using same |
US5714110A (en) * | 1993-09-20 | 1998-02-03 | Scimed Life Systems, Inc. | Process improvements for preparing catheter balloons |
US5746968A (en) * | 1994-10-20 | 1998-05-05 | Interventional Technologies, Inc. | Method for manufacturing a high strength angioplasty balloon |
US5807520A (en) * | 1995-11-08 | 1998-09-15 | Scimed Life Systems, Inc. | Method of balloon formation by cold drawing/necking |
US5849846A (en) * | 1994-07-25 | 1998-12-15 | Advanced Cardiovascular Systems, Inc. | Balloons for medical catheters |
US5853408A (en) * | 1992-08-20 | 1998-12-29 | Advanced Cardiovascular Systems, Inc. | In-vivo modification of the mechanical properties of surgical devices |
US5871468A (en) * | 1996-04-24 | 1999-02-16 | Medtronic, Inc. | Medical catheter with a high pressure/low compliant balloon |
US6093463A (en) | 1997-12-12 | 2000-07-25 | Intella Interventional Systems, Inc. | Medical devices made from improved polymer blends |
US6099926A (en) | 1997-12-12 | 2000-08-08 | Intella Interventional Systems, Inc. | Aliphatic polyketone compositions and medical devices |
US6165207A (en) | 1999-05-27 | 2000-12-26 | Alsius Corporation | Method of selectively shaping hollow fibers of heat exchange catheter |
US6171278B1 (en) * | 1994-03-02 | 2001-01-09 | Scimed Life Systems, Inc. | Block copolymer elastomer catheter balloons |
US6193738B1 (en) | 1998-05-11 | 2001-02-27 | Scimed Life Systems, Inc. | Balloon cones and waists thinning methodology |
US6242063B1 (en) | 1997-09-10 | 2001-06-05 | Scimed Life Systems, Inc. | Balloons made from liquid crystal polymer blends |
US6284333B1 (en) | 1997-09-10 | 2001-09-04 | Scimed Life Systems, Inc. | Medical devices made from polymer blends containing low melting temperature liquid crystal polymers |
US6287506B1 (en) | 1998-07-09 | 2001-09-11 | Schneider (Usa) Inc. | Method for reducing dilation balloon cone stiffness |
US6287326B1 (en) | 1999-08-02 | 2001-09-11 | Alsius Corporation | Catheter with coiled multi-lumen heat transfer extension |
US6299599B1 (en) | 1999-02-19 | 2001-10-09 | Alsius Corporation | Dual balloon central venous line catheter temperature control system |
US6358227B1 (en) | 1997-09-10 | 2002-03-19 | Scimed Life Systems, Inc. | Dilatation catheter balloon made from pen based homopolymer or random copolymer |
US6360577B2 (en) | 1999-09-22 | 2002-03-26 | Scimed Life Systems, Inc. | Apparatus for contracting, or crimping stents |
US6368304B1 (en) | 1999-02-19 | 2002-04-09 | Alsius Corporation | Central venous catheter with heat exchange membrane |
US6393320B2 (en) | 1999-02-19 | 2002-05-21 | Alsius Corporation | Method for treating cardiac arrest |
US6395208B1 (en) * | 1999-01-25 | 2002-05-28 | Atrium Medical Corporation | Method of making an expandable fluoropolymer device |
US6406457B1 (en) * | 1994-03-02 | 2002-06-18 | Scimed Life Systems, Inc. | Block copolymer elastomer catheter balloons |
US6419643B1 (en) | 1998-04-21 | 2002-07-16 | Alsius Corporation | Central venous catheter with heat exchange properties |
US6447474B1 (en) | 1999-09-15 | 2002-09-10 | Alsius Corporation | Automatic fever abatement system |
US6450990B1 (en) | 1998-08-13 | 2002-09-17 | Alsius Corporation | Catheter with multiple heating/cooling fibers employing fiber spreading features |
US6458150B1 (en) | 1999-02-19 | 2002-10-01 | Alsius Corporation | Method and apparatus for patient temperature control |
US6465067B1 (en) | 1998-03-04 | 2002-10-15 | Scimed Life Systems, Inc. | Composition and process for manufacturing PBT catheter balloons |
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US6500146B1 (en) | 1988-10-04 | 2002-12-31 | Cordis Corporation | Balloons for medical devices and fabrication thereof |
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US6582398B1 (en) | 1999-02-19 | 2003-06-24 | Alsius Corporation | Method of managing patient temperature with a heat exchange catheter |
US6589271B1 (en) | 1998-04-21 | 2003-07-08 | Alsius Corporations | Indwelling heat exchange catheter |
US6623516B2 (en) | 1992-08-13 | 2003-09-23 | Mark A. Saab | Method for changing the temperature of a selected body region |
US6629350B2 (en) | 2000-06-08 | 2003-10-07 | Tom Motsenbocker | Stent crimping apparatus and method |
US20040039410A1 (en) * | 2002-08-22 | 2004-02-26 | Brooke Ren | High-strength balloon with tailored softness |
US6716236B1 (en) | 1998-04-21 | 2004-04-06 | Alsius Corporation | Intravascular catheter with heat exchange element having inner inflation element and methods of use |
US20040065754A1 (en) * | 2002-03-15 | 2004-04-08 | Arko Development Ltd. | Bubble generating assembly |
US20040146670A1 (en) * | 2003-01-27 | 2004-07-29 | Albert Chin | Multilayer balloon catheter |
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US20050059989A1 (en) * | 2003-09-17 | 2005-03-17 | Scimed Life Systems, Inc. | Balloon assembly with a torque |
US6946092B1 (en) | 2001-09-10 | 2005-09-20 | Scimed Life Systems, Inc. | Medical balloon |
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US20050267408A1 (en) * | 2004-05-27 | 2005-12-01 | Axel Grandt | Catheter having first and second guidewire tubes and overlapping stiffening members |
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US20070016165A1 (en) * | 2004-05-27 | 2007-01-18 | Randolf Von Oepen | Catheter having plurality of stiffening members |
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US7749585B2 (en) | 1996-10-08 | 2010-07-06 | Alan Zamore | Reduced profile medical balloon element |
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US7815627B2 (en) | 2004-05-27 | 2010-10-19 | Abbott Laboratories | Catheter having plurality of stiffening members |
US7887557B2 (en) | 2003-08-14 | 2011-02-15 | Boston Scientific Scimed, Inc. | Catheter having a cutting balloon including multiple cavities or multiple channels |
US7892469B2 (en) | 1998-04-21 | 2011-02-22 | Advanced Cardiovascular Systems, Inc. | Method of making a non-compliant balloon for a catheter |
US7947059B2 (en) | 2000-03-02 | 2011-05-24 | Boston Scientific Scimed, Inc. | Multilayer medical device |
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