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WO1999013924A2 - Ballonnets de catheters en copolymere sequence d'amide et de polyether - Google Patents

Ballonnets de catheters en copolymere sequence d'amide et de polyether Download PDF

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Publication number
WO1999013924A2
WO1999013924A2 PCT/US1998/019627 US9819627W WO9913924A2 WO 1999013924 A2 WO1999013924 A2 WO 1999013924A2 US 9819627 W US9819627 W US 9819627W WO 9913924 A2 WO9913924 A2 WO 9913924A2
Authority
WO
WIPO (PCT)
Prior art keywords
balloon
nylon
polyamide
catheter
block copolymer
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.)
Ceased
Application number
PCT/US1998/019627
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English (en)
Other versions
WO1999013924A3 (fr
Inventor
Jeong S. Lee
Debashish Dutta
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Abbott Cardiovascular Systems Inc
Original Assignee
Advanced Cardiovascular Systems Inc
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Advanced Cardiovascular Systems Inc filed Critical Advanced Cardiovascular Systems Inc
Priority to EP98948371A priority Critical patent/EP1011744A2/fr
Priority to JP2000511536A priority patent/JP2001516621A/ja
Priority to CA002303159A priority patent/CA2303159A1/fr
Publication of WO1999013924A2 publication Critical patent/WO1999013924A2/fr
Publication of WO1999013924A3 publication Critical patent/WO1999013924A3/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/04—Macromolecular materials
    • A61L29/06—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
    • 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]
    • Y10T428/1386—Natural or synthetic rubber or rubber-like compound containing

Definitions

  • This invention generally relates to intravascular catheters, such as balloon dilatation catheters used in percutaneous transluminal coronary angioplasty (PTCA).
  • PTCA percutaneous transluminal coronary angioplasty
  • a balloon dilatation catheter is advanced into the patient's coronary artery and the balloon on the catheter is inflated within the stenotic region of the patient's artery to open up the arterial passageway and thereby increase the blood flow there through.
  • a guiding catheter having a preshaped distal tip is first percutaneously introduced into the cardiovascular system of a patient by the Seldinger technique through the brachial or femoral arteries. The catheter is advanced until the preshaped distal tip of the guiding catheter is disposed within the aorta adjacent the ostium of the desired coronary artery, and the distal tip of the guiding catheter is then maneuvered into the ostium.
  • a balloon dilatation catheter may then be advanced through the guiding catheter into the patient's coronary artery until the balloon on the catheter is disposed within the stenotic region of the patient's artery.
  • the balloon is inflated to open up the arterial passageway and increase the blood flow through the artery.
  • the inflated diameter of the balloon is approximately the same diameter as the native diameter of the body lumen being dilated so as to complete the dilatation but not over expand the artery wall.
  • Stents may also be used to repair vessels having an intimal flap or dissection or to generally strengthen a weakened section of a vessel.
  • Stents are usually delivered to a desired location within a coronary artery in a contracted condition on a balloon of a catheter which is similar in many respects to a balloon angioplasty catheter, and expanded to a larger diameter by expansion of the balloon. The balloon is deflated to remove the catheter and the stent left in place within the artery at the site of the dilated lesion. See for example, U.S. Pat. No. 5,507,768 (Lau et al.) and U.S. Pat. No. 5,458,615 (Klemm et al.), which are incorporated herein by reference.
  • an over-the-wire type balloon dilatation catheter One type of catheter frequently used in PTCA procedures is an over-the-wire type balloon dilatation catheter.
  • a guidewire is usually inserted into an inner lumen of the dilatation catheter before it is introduced into the patient's vascular system and then both are introduced into and advanced through the guiding catheter to its distal tip which is seated within the ostium.
  • the guidewire is first advanced out the seated distal tip of the guiding catheter into the desired coronary artery until the distal end of the guidewire extends beyond the lesion to be dilatated.
  • the dilatation catheter is then advanced out of the distal tip of the guiding catheter into the patient's coronary artery, over the previously advanced guidewire, until the balloon on the distal extremity of the dilatation catheter is properly positioned across the lesion to be dilatated.
  • the balloon is inflated one or more times to a predetermined size with radiopaque liquid at relatively high pressures (e.g., generally 4-12 atmospheres) to dilate the stenosed region of a diseased artery.
  • relatively high pressures e.g., generally 4-12 atmospheres
  • This dilatation catheter has a short guidewire receiving sleeve or inner lumen extending through a distal portion of the catheter.
  • the sleeve or inner lumen extends proximally from a first guidewire port in the distal end of the catheter to a second guidewire port in the catheter spaced proximally from the inflatable member of the catheter.
  • a slit may be provided in the wall of the catheter body which extends distally from the second guidewire port, preferably to a location proximal to the proximal end of the inflatable balloon.
  • This catheter which can take the form of an over-the-wire catheter or a rapid exchange type catheter, has one or more perfusion ports proximal to the dilatation balloon in fluid communication with an guidewire receiving inner lumen extending to the distal end of the catheter.
  • One or more perfusion ports are preferably provided in the catheter distal to the balloon which are also in fluid communication with the inner lumen extending to the distal end of the catheter. This provides oxygenated blood downstream from the inflated balloon to thereby prevent or minimize ischemic conditions in tissue distal to the catheter.
  • the perfusion of blood distal to the inflated balloon allows for long term dilatations, e.g. 30 minutes or even several hours or more.
  • the balloons for prior dilatation catheters utilized in angioplasty procedures generally have been formed of relatively inelastic polymeric materials such as polyvinyl chloride, polyethylene, polyethylene terephthalate (PET), polyolefinic ionomers, and nylon.
  • An advantage of such inelastic materials when used in catheter balloons is that the tensile strength, and therefore the mean rupture pressure, of the balloon is high.
  • Catheter balloons must have high tensile strength in order to exert sufficient pressure on the stenosed vessel and effectively open the patient's passageway. Consequently the high strength balloon can be inflated to high pressures without a risk that the balloon will burst during pressurization.
  • the wall thickness of high strength balloons can be made thin, in order to decrease the catheter profile, without a risk of bursting.
  • non-compliant materials having the least elasticity are also classified as “non-compliant” and “semi-compliant” materials, and include PET and nylon. Such non-compliant material exhibits little expansion in response to increasing levels of inflation pressure. Because the non-compliant material has a limited ability to expand, the uninflated balloon must be made sufficiently large that, when inflated, the balloon has sufficient working diameter to compress the stenosis and open the patient's passageway. However, a large profile non-compliant balloon can make the catheter difficult to advance through the patient's narrow vasculature because, in a uninflated condition, such balloons form flat or pancake shape wings which extend radially outward. Therefore, some compliance is desirable in an angioplasty catheter balloon.
  • balloons formed of material with high compliance have increased softness, which improves the ability of the catheter to track the tortuous vasculature of the patient and cross the stenosis, to effectively position the balloon at the stenosis.
  • the softness of a balloon is expressed in terms of the balloon modulus, where a relatively soft balloon has a relatively low flexural modulus of less than about 150,000 psi (1034 MPa).
  • the present invention satisfies these and other needs.
  • the invention is directed to an inflatable member such as a balloon which is formed at least in part of a polyamide/polyether block copolymer thermoplastic elastomer, commonly referred to as polyether block amide (PEBA).
  • PEBA polyether block amide
  • a balloon catheter of the invention generally comprises a catheter having an elongated shaft with an inflatable balloon formed of PEBA thermoplastic elastomer on a distal portion of the catheter.
  • Suitable PEBA balloon materials include, but are not limited to, PEBAX®, a polyamide/polyether polyester available from Atochem and described in U.S. Patents 4,331 ,786 and 4,332,920 (Foy et al.), which are incorporated herein by reference.
  • the presently preferred PEBA copolymer is polyamide/polyether polyester copolymer.
  • the presently preferred balloon is formed from 100% PEBA.
  • the balloon can be formed of a blend of PEBA with one or more different polymeric materials. Suitable polymeric materials for blending with PEBA include those polymers listed above used to make balloons for prior dilatation catheters, such as nylon.
  • the balloon is a single polymeric layer.
  • the balloon may also be multilayered, where the balloon is formed by coextruding two or more layers with one or more layers formed at least in part of PEBA.
  • Various designs for balloon catheters well known in the art may be used in the catheter of the invention having a balloon formed at least in part PEBA.
  • the catheter may be a conventional over-the-wire dilatation catheter for angioplasty having a guidewire receiving lumen extending the length of the catheter shaft from a guidewire port in the proximal end of the shaft, or a rapid exchange dilatation catheter having a short guidewire lumen extending to the distal end of the shaft from a guidewire port located distal to the proximal end of the shaft.
  • the catheter may be used to deliver a stent mounted on the catheter balloon.
  • the balloon of the invention formed of PEBA thermoplastic elastomer, combines improved softness and tensile strength, to provide low profile balloon catheters having excellent ability to tract the patient's vasculature, cross the stenosis, and compress the stenosis to open the patient's vessel.
  • Fig. 1 is an elevational view partially in section of the catheter of the invention showing the balloon in an unexpanded state.
  • Fig. 2 is a transverse cross sectional view of the catheter of Fig. 1 taken along lines 2-2.
  • Fig. 3 is a transverse cross sectional view of the catheter of Fig. 1 taken along lines 3-3.
  • Fig. 4 is an elevational view partially in section of the catheter of the invention.
  • Fig. 5 is a transverse cross sectional view of the catheter of Fig. 4 taken along lines 5-5.
  • the catheter 10 of the invention generally includes a an elongated catheter shaft 11 having a proximal section 12 and distal section 13, an inflatable balloon 14 formed at least in part of PEBA on the distal section 13 of the catheter shaft 11 , and an adapter 17 mounted on the proximal section 12 of shaft 11 to direct inflation fluid to the interior of the inflatable balloon.
  • Figs. 2 and 3 illustrate transverse cross sections of the catheter shown in Fig. 1 , taken along lines 2-2 and 3-3 respectively.
  • the intravascular catheter 10 of the invention is an over-the-wire catheter, and is illustrated within a patient's body lumen 18 with the balloon 14 in an unexpanded state.
  • the catheter shaft 11 has an outer tubular member 19 and an inner tubular member 20 disposed within the outer tubular member and defining, with the outer tubular member, inflation lumen 21.
  • Inflation lumen 21 is in fluid communication with the interior chamber 15 of the inflatable balloon 14.
  • the inner tubular member 20 has an inner lumen 22 extending therein, which is configured to slidably receive a guidewire 23 suitable for advancement through a patient's coronary arteries.
  • the distal extremity of the inflatable balloon 14 is sealingly secured to the distal extremity of the inner tubular member 20 and the proximal extremity of the balloon is sealingly secured to the distal extremity of the outer tubular member 19.
  • the balloons of the invention are formed at least in part of polyamide/polyether block (PEBA) copolymers.
  • PEBA polyamide/polyether block
  • the presently preferred PEBA copolymers have polyamide and polyether segments linked through ester linkages, i.e. polyamide/polyether polyesters.
  • other linkages such as amide linkages, can also be used.
  • Polyamide/polyether polyester block copolymers are made by a molten state polycondensation reaction of a dicarboxylic polyamide and a polyether diol. The result is a short chain polyester made up of blocks of polyamide and polyether. The polyamide and polyether blocks are not miscible.
  • the materials are characterized by a two phase structure having a thermoplastic region that is primarily polyamide and an elastomer region that is rich in polyether.
  • the polyamide segments are semicrystalline at room temperature.
  • the generalized chemical formula for these polyamide/polyether polyester block copolymers may be represented by the following formula:
  • PA is a polyamide hard segment
  • PE is a polyether soft segment
  • the repeating number n is between 5 and 10.
  • the polyamide hard segment is a polyamide of C 6 or higher, preferably C 10 -C 12 , carboxylic acids; C 6 or higher, preferably C 10 -C 12 , organic diamines; or C 6 or higher, preferably C 10 -C 12 , aliphatic ⁇ - amino- ⁇ -acids.
  • the percentage by weight of the block copolymer attributable to the polyamide hard segments is between about 50% to about 95%.
  • the polyether soft segment is a polyether of C 2 -C 10 diols, preferably C 4 -C 6 diols.
  • the block copolymer has a flexural modulus of less than about 150,000 psi (1034 MPa), preferably less than 120,000 psi (827 MPa).
  • the polyamide segments are suitably aliphatic polyamides, such as nylons
  • nylon 12 segments Most preferably they are nylon 12 segments.
  • the polyamide segments may also be based on aromatic polyamides but in such case significantly lower compliance characteristics are to be expected.
  • the polyamide segments are relatively low molecular weight, generally within the range of 500-8,000, more preferably 2,000-6,000, most preferably about 3,000-5,000. Another range which is of interest is 300-15,000.
  • the polyether segments are aliphatic polyethers having at least 2 and no more than 10 linear saturated aliphatic carbon atoms between ether linkages. More preferably the ether segments have 4-6 carbons between ether linkages, and most preferably they are poly(tetramethylene ether) segments. Examples of other polyethers which may be employed in place of the preferred tetramethylene ether segments include polyethylene glycol, polypropylene glycol, poly(pentamethylene ether) and poly(hexamethylene ether). The hydrocarbon portions of the polyether may be optionally branched. An example is the polyether of 2-ethylhexane diol. Generally such branches will contain no more than two carbon atoms. The molecular weight of the polyether segments is suitably between about 400 and 2,500, preferably between 650 and 1 ,000. Another range which is of interest is 200- 6,000.
  • the weight ratio of polyamide to polyether in the polyamide/polyether polyesters used in the invention desirably should be in the range of 50/50 to 95/5, preferably between 60/30 and 92/08, more preferably, between 70/30 and 90/10.
  • Polyamide/polyether polyesters are sold commercially under the PEBAX trademark by Atochem North America, Inc., Philadelphia, PA.
  • a suitable polymer grade for the intravascular balloon catheter of the invention is the PEBAX® 33 series.
  • the presently preferred PEBAX® polymers have a hardness of Shore D durometer of at least about 60D, preferably between about 60D to about 72D, i.e. PEBAX® 6033 and 7233.
  • the presently preferred PEBAX® polymers have a hardness of Shore D durometer of at least about 35 D, preferably between about 35D to about 72D, i.e. PEBAX® 3533 and 7233.
  • the PEBAX® 7033 and 6333 polymers are made up of nylon 12 segments and polytetramethylene ether segments in about 90/10 and about 80/20 weight ratios, respectively.
  • the average molecular weight of the individual segments of nylon 12 is in the range of about 3,000-5,000 grams/mole and of the polytetramethylene ether segments are in ranges of about 750-1 ,250 for the 6333 polymer and about 500-800 for the 7033 polymer.
  • the intrinsic viscosities of these polymers are in the range of 1.33 to 1.50 dl/g.
  • balloons of PEBAX® 7033 type polymer exhibit borderline non-compliant to semi-compliant behavior and balloons of Pebax® 6333 type polymer show semi-compliant to compliant distention behavior, depending on the balloon forming conditions.
  • PEBAX®-type polyamide/polyether polyesters are most preferred, it is also possible to use other PEBA polymers with the physical properties specified herein and obtain similar compliance, strength and softness characteristics in the finished balloon.
  • the presently preferred PEBA material has an elongation at failure at room temperature of at least about 150%, preferably about 300% or higher, and an ultimate tensile strength of at least 6,000 psi.
  • the balloon has sufficient strength to withstand the inflation pressures needed to inflate the balloon and compress a stenosis in a patient's vessel.
  • the burst pressure of the balloon is at least about 10 ATM, and is typically about 16-21 ATM.
  • the wall strength of the balloon is at least about 15,000 psi (103 MPa), and typically from about 25,000 psi (172 Mpa) to about 35,000 psi (241 MPa).
  • the inflatable balloon 14 shown in Fig. 1 is formed of a single layer of polymeric material.
  • the balloon may be 100% PEBA or a PEBA/polymer blend.
  • the presently preferred polymer blend is a PEBAX®/nylon blend, and the preferred weight percent of nylon is from about 30% to about 95% of the total weight.
  • the inflatable balloon 14 may also have multiple layers formed from coextruded tubing, in which one or more layers is at least in part formed from PEBA.
  • the multilayered balloon is made from coextruded tubing have at least a nylon layer and a PEBA layer.
  • the presently preferred PEBA is PEBAX®, and the presently preferred nylon is nylon 11 , nylon 12, or blends thereof.
  • the PEBAX® may be the inner layer or the outer layer of the balloon.
  • the balloon of the invention can be produced by conventional techniques for producing catheter inflatable members, such as blow molding, and may be preformed by stretching a straight tube before the balloon is blown.
  • the balloons may be formed by expansion of tubing, as for example at a hoop ratio of between 3 and 8.
  • the presently preferred PEBA balloon material is not crosslinked.
  • the bonding of the balloon to the catheter may be by conventional techniques, such as adhesives and fusion with compatibilizers.
  • Fig. 2 showing a transverse cross section of the catheter shaft 11 , illustrates the guidewire receiving lumen 22 and inflation lumen 21.
  • the balloon 14 can be inflated by radiopaque fluid from an inflation port 24, from inflation lumen 21 contained in the catheter shaft 11 , or by other means, such as from a passageway formed between the outside of the catheter shaft and the member forming the balloon, depending on the particular design of the catheter.
  • the details and mechanics of balloon inflation vary according to the specific design of the catheter, and are well known in the art.
  • the length of the balloon 14 may be about 0.5 cm to about 6 cm, preferably about 1.0 cm to about 4.0 cm.
  • the balloon working length outer diameter at nominal pressure e.g. 6-8 ATM
  • the balloon working length outer diameter at nominal pressure is generally about 0.15 cm to about 0.4 cm, and typically about 0.3 cm, although balloons having an outer diameter of about 1 cm may also be used.
  • the single wall thickness is about 0.0004 inches (in) (0.0102 mm) to about 0.0015 in (0.0381 mm), and typically about .0006 in (0.0152 mm).
  • the nylon layer single wall thickness is about .0003 in (0.0076 mm) to about .0006 in (0.0152 mm)
  • the PEBAX layer is about .0002 in (0.0051 mm) to about .0005 in (0.0127 mm).
  • a stent 16 is disposed about the balloon 14 for delivery within patient's vessel.
  • Fig. 5 illustrates a transverse cross section of the catheter shown in Fig. 4, taken along line 5-5.
  • the stent 16 may be any of a variety of stent materials and forms designed to be implanted by an expanding member, see for example U.S. Patent 5,514,154 (Lau et al.) and 5,443,500 (Sigwart), incorporated by reference.
  • the stent material may be stainless steel, a NiTi alloy, a plastic material, or various other materials.
  • the stent is shown in an unexpanded state in Fig. 4.
  • the stent has a smaller diameter for insertion and advancement into the patient's lumen, and is expandable to a larger diameter for implanting in the patient's lumen.
  • the balloon of the invention formed at least in part of PEBA has improved abrasion resistance, useful in stent delivery, due to the PEBA.
  • a balloon used for stent delivery preferably has the PEBA layer as the outer layer, to provide improved resistance to puncture by the stent. Additionally, the stent retention force is improved when the balloon is formed by coextrusion.
  • PEBAX® 7033 was extruded into tubular stock having 0.035 in (0.889 mm) outer diameter (OD) and 0.019 in (0.483 mm) inner diameter (ID). The tubing was necked on one side at room temperature to ID of 0.018 in (0.457 mm). The tubing was then made into 20 balloons using a glass mold at a temperature of 242 °F (116.7 °C) inside the mold and a blow pressure of 340 psi (2343 kPa). The balloons had an OD of 3 mm and a length of 20 mm. The balloon working length had a wall thickness of 0.0006 in (0.0152 mm) to 0.0007 in (0.0178 mm). The mean rupture pressure of the balloons was found to be 310 psi (2136 kPa) with a standard deviation of 17.21 psi (119 kPa).
  • PEBAX® 6033 and nylon 12 was coextruded into two layered tubing, with PEBAX® as the outer layer and nylon as the inner layer.
  • the tubing had a 0.035 in (0.889 mm) OD and a 0.0195 in (0.495 mm) ID, and a nylon layer thickness of 0.004 in (0.102 mm) and a PEBAX® layer thickness of 0.002 (0.051 mm).
  • the tubing was then made into 20 balloons using a glass mold as in Example 1 , at a temperature of 235.5 °F (113 °C) inside the mold and a blow pressure of 300 psi (2067 kPa).
  • the balloon working length had a wall thickness of 0.0005 in (0.0127 mm) to 0.00065 in (0.0165 mm).
  • the mean rupture pressure of the balloons was found to be 317 psi (2184 kPa) with a standard deviation of 23.3 psi (161 kPa).
  • EXAMPLE 3 Twenty percent PEBAX® 7233 and 80% nylon 12 was blended in a single screw extruder, and extruded into tubular stock having 0.0325 in (0.826 mm) OD and 0.015 in (0.381 mm) ID. The tubing was then made into 10 balloons using a glass mold as in Example 1 , at a temperature of 320 °F (160 °C) inside the mold and a blow pressure of 225 psi (1550 kPa). The balloon working length had a wall thickness of 0.00045 in (0.0114 mm). The mean rupture pressure of the balloons was found to be 280 psi (1929 kPa).

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Abstract

L'invention a pour objet un élément gonflable tel qu'un ballonnet qui se compose au moins en partie d'un élastomère thermoplastique de copolymère séquencé de polyamide/polyéther, généralement appelé copolymère séquencé d'amide et de polyéther (PEBA). Le copolymère préféré de PEBA est un copolymère de polyester de polyéther/polyamide, tel que du PEBAX3. Le ballonnet selon l'invention présente une résistance à la traction élevée, un allongement à la rupture important et un module de flexion faible. Le ballonnet peut être formé comme simple couche de PEBA, ou comme un coextrudat multicouches présentant au moins une couche de PEBA. Le ballonnet peut être réalisé à 100 % en PEBA ou un mélange de PEBA avec un autre polymère, comme du nylon.
PCT/US1998/019627 1997-09-17 1998-09-17 Ballonnets de catheters en copolymere sequence d'amide et de polyether Ceased WO1999013924A2 (fr)

Priority Applications (3)

Application Number Priority Date Filing Date Title
EP98948371A EP1011744A2 (fr) 1997-09-17 1998-09-17 Ballonnets de catheters en copolymere sequence d'amide et de polyether
JP2000511536A JP2001516621A (ja) 1997-09-17 1998-09-17 ポリエーテルブロックアミドカテーテルバルーン
CA002303159A CA2303159A1 (fr) 1997-09-17 1998-09-17 Ballonnets de catheters en copolymere sequence d'amide et de polyether

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US93290897A 1997-09-17 1997-09-17
US08/932,908 1997-09-17

Publications (2)

Publication Number Publication Date
WO1999013924A2 true WO1999013924A2 (fr) 1999-03-25
WO1999013924A3 WO1999013924A3 (fr) 1999-06-10

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PCT/US1998/019627 Ceased WO1999013924A2 (fr) 1997-09-17 1998-09-17 Ballonnets de catheters en copolymere sequence d'amide et de polyether

Country Status (5)

Country Link
US (1) US20020018866A1 (fr)
EP (1) EP1011744A2 (fr)
JP (1) JP2001516621A (fr)
CA (1) CA2303159A1 (fr)
WO (1) WO1999013924A2 (fr)

Cited By (27)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2001029450A (ja) * 1999-05-18 2001-02-06 Kanegafuchi Chem Ind Co Ltd 医療用ポリマーブレンド材料およびこの材料を用いた医療用バルーン
WO2001039810A1 (fr) * 1999-12-01 2001-06-07 Advanced Cardiovascular Systems, Inc. Ballonnet de dispositif medical
WO2002058913A1 (fr) * 2001-01-24 2002-08-01 Scimed Life Systems, Inc Procede de fabrication de ballonnets de catheters par soufflage de preformes humides
US6579940B1 (en) 1999-10-28 2003-06-17 Edwards Lifesciences Corporation Thermoplastic elastomeric material as a replacement for natural rubber latex
US6613838B1 (en) 2000-08-30 2003-09-02 Edwards Lifesciences Corporation Synthetic rubber elastomers as replacements for natural rubber latex
WO2004024204A1 (fr) * 2002-09-11 2004-03-25 Scimed Life Systems, Inc. Dispositifs medicaux sterilises par rayonnement comprenant des polymeres radiosensibles
JP2004517676A (ja) * 2000-03-02 2004-06-17 シメッド　ライフ　システムズ　インコーポレイテッド 多層医療器具
WO2005066241A1 (fr) * 2003-12-19 2005-07-21 Advanced Cardiovascular Systems, Inc. Polymeres de polyamide/polyethylene-glycol biobenefiques, conçus pour etre utilises avec des protheses endovasculaires a elution de medicaments
US7150853B2 (en) * 2001-11-01 2006-12-19 Advanced Cardiovascular Systems, Inc. Method of sterilizing a medical device
JP2007537827A (ja) * 2004-05-20 2007-12-27 ボストン サイエンティフィック リミテッド 多層を有する医療用デバイス
WO2007120323A3 (fr) * 2005-12-16 2008-03-13 Medtronic Vascular Inc Ballonnets médicaux à double couche
WO2008073695A3 (fr) * 2006-12-11 2009-04-23 Medtronic Vascular Inc Ballons médicaux à double couche
WO2010062793A2 (fr) 2008-11-26 2010-06-03 Abbott Cardiovascular Systems Inc. Tube de cathéter à faible élasticité
WO2010027588A3 (fr) * 2008-09-03 2010-10-14 Boston Scientific Scimed, Inc. Ballonnet medical multicouche
US8052638B2 (en) 2008-11-26 2011-11-08 Abbott Cardiovascular Systems, Inc. Robust multi-layer balloon
WO2014205158A1 (fr) * 2013-06-20 2014-12-24 Covidien Lp Ballonnet pour dispositif médical
US9056190B2 (en) 2006-06-30 2015-06-16 Abbott Cardiovascular Systems Inc. Balloon catheter tapered shaft having high strength and flexibility and method of making same
WO2015155489A1 (fr) * 2014-04-11 2015-10-15 Arkema France Utilisation de peba à blocs longs pour la fabrication de tout ou partie d'un cathéter
US9205232B2 (en) 2011-09-29 2015-12-08 Terumo Kabushiki Kaisha Balloon for catheter and balloon catheter
WO2016007928A1 (fr) * 2014-07-10 2016-01-14 Interface Associates, Inc. Ballonnets emboîtés pour applications médicales et leurs procédés de fabrication
US9707380B2 (en) 2012-07-05 2017-07-18 Abbott Cardiovascular Systems Inc. Catheter with a dual lumen monolithic shaft
US9833600B2 (en) 2005-12-16 2017-12-05 Interface Associates, Inc. Methods for manufacturing multi-layer balloons for medical applications
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US20020018866A1 (en) 2002-02-14
WO1999013924A3 (fr) 1999-06-10

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