|Publication number||US20040191443 A1|
|Application number||US 10/822,182|
|Publication date||Sep 30, 2004|
|Filing date||Apr 9, 2004|
|Priority date||Sep 25, 1989|
|Also published as||CA2025962A1, CA2025962C, DE69002295D1, DE69002295T2, EP0420488A1, EP0420488B1, US5270086, US6132824, US20040207127|
|Publication number||10822182, 822182, US 2004/0191443 A1, US 2004/191443 A1, US 20040191443 A1, US 20040191443A1, US 2004191443 A1, US 2004191443A1, US-A1-20040191443, US-A1-2004191443, US2004/0191443A1, US2004/191443A1, US20040191443 A1, US20040191443A1, US2004191443 A1, US2004191443A1|
|Original Assignee||Schneider (Usa) Inc., A Corporation|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (40), Referenced by (18), Classifications (37), Legal Events (1)|
|External Links: USPTO, USPTO Assignment, Espacenet|
 I. Field of the Invention
 This invention relates generally to balloon catheters, and more particularly to a method for fabricating a multi-layer balloon composite exhibiting enhanced characteristics attributable to the properties of the individual layers.
 II. Discussion of the Prior Art
 As an alternative to open-heart, coronary bypass surgery, a technique referred to coronary transluminal angioplasty has been developed following the pioneering introduction of the technique by A. Gruntzig. In carrying out this procedure, a dilatation catheter having an inflatable expander member (balloon) on the distal end thereof is routed through the vascular system to a location within a coronary artery containing a stenotic lesion. Following placement of the expander member across the lesion, a fluid is introduced into the proximal end of the catheter and is used to inflate the expander member to a predetermined relatively high pressure whereby the lesion is compressed into the vessel wall restoring patency to the previously occluded vessel.
 It is desirable that the composite expander member exhibit the following characteristics:
 1. High burst (tensile) strength;
 2. Low radial expansion at elevated pressures;
 3. Ease of bonding to a catheter body;
 4. Failure characteristics avoiding pinhole ruptures; and
 5. Low coefficient of friction.
 The Schjeldahl et al. U.S. Pat. No. 4,413,989 owned by applicants' assignee discloses a coronary transluminal angioplasty catheter in which the expander member is formed from polyethylene terephthalate in a drawing and blow molding process so as to provide biaxial orientation to the material. Such PET balloons are found to exhibit the desirable property of high burst strength and relatively low radial expansion when inflated to seven atmospheres or more. However, because the catheter body itself is generally fabricated from a formulation containing silicon rubber, polyethylene, PET or polyurethane, a problem exists when attempts are made to bond the expander member to the distal end portion of the catheter body. The PET polyester balloon tends not to adhere easily to the catheter body especially in a thermal bonding process.
 Moreover, experience with polyethylene, PVC and polypropylene expansion members has shown that at relatively high pressures, pinhole leaks form which may create a high velocity jet of inflation fluid capable of perforating the blood vessel when it impinges on the vessel wall. Thus it would be desirable if the expander member can be fabricated in such a way that it exhibits a controlled mode of failure, i.e., a rapid rupture so that the pressure is released over a significant area in a short time frame.
 The above-listed desirable characteristics are achieved in accordance with the present invention by forming a multi-layer balloon where the individual layers afford a desirable property to the composite. It has been found that a layer of medium or relatively high melt temperature material which also exhibits high tensile strength with relatively low distensibility can be used to provide the required high burst or tensile strength and low radial expansion at high pressures required by the expander member in a composite structure. This layer may be referred to as the tensile layer or tensile ply. It may be a biaxially-oriented film of relatively high crystallinity.
 In the composite structure, the tensile layer is combined as an outer layer with a chemically and physically compatible adhesion or bonding inner layer which is fabricated from materials having superior glue bonding or melt bonding characteristics. The bonding layer also must have good interlayer adhesion characteristics with the material used for the tensile layer. The bonding layer imparts the necessary adhesion properties to properly bond the expander member to the distal end portion of the catheter body. If melt bonding is the desired mode, the material of the bonding layer should have a lower melting point than that of the tensile layer so that melt bonding of the composite may be readily achieved in the fabrication process with minimal effect on the tensile ply. In this regard, it should be noted that the bonding layer may or may not be continuous or coextensive with the entire inner surface of the tensile layer inasmuch as it is required generally only in the vicinity of the expander/catheter interface surfaces.
 Examples of materials exhibiting the required high tensile, low distensibility and having medium melt temperatures include certain copolymers such as ABS (acrylonitrile-butadiene-styrene), ABS/nylon, ABS/polyvinyl chloride (PVC) and ABS/polycarbonate. Such materials having high melt temperatures include acrylonitrile copolymer, polyacrylamiede, polyacrylate and polyacrylsulfone. Other materials having suitable characteristics include high melt temperature polyesters such as polyethylene terephthalate (PET), polybutylene terephthalate (PBT), polyethylene naphthalate (PEN), liquid crystal polymer (LCP), polyester/polycaprolactone and polyester/polyadipate; and high melt temperature polyethers including polyetheretherketone (PEEK), polyethersulfone (PES), polyetherimide (PEI) and polyetherketone (PEK), polymenthylpentene, polyphenylene ether, polyphenylene sulfide, and styrene acrylonitrile (SAN). It should be noted that LCP has a very high melt temperature and SAN, a lower melt temperature than the other listed polyethers. Additional compounds having the required tensile properties which have a medium melt temperature include polyamides such as nylon 6, nylon 6/6, nylon 6/66, nylon 6/9, nylon 6/10, nylon 6/12, nylon 11 and nylon 12.
 Suitable adhesion materials for the bonding layer having a high distensibility but excellent melt bond and glue adhesion properties with relatively low melt temperatures include ethylene, propylene, ethylene vinylacetate and ethylene vinyl alcohol (EVA), various ionomers, polyethylene type I-IV, polyolefins, polyurethane, polyvinyl chloride, and polysiloxanes (silicones). Those with low to medium melt temperatures include fluorocarbons such as polychlorotriethylene (CTFE), poly[ethylene-co-chlorotrifluoroethylene] (ECTFE) copolymer ethylene tetrafluoroethylene (ETFE), copolymer tetrafluoroethylene and hexafluoropropylene (FEP), perfluoroalkane (PFA) and poly[vinylidene fluoride] (PVDF).
 It will be appreciated that the particular combination chosen would depend on the particular application and particular catheter involved, and that an array of multilayer expanders of different composition combinations particularly applicable to different situations can be produced. In addition, specific properties required for addressing a specific stenosis could be utilized to produce a tailor-made expander.
 More particularly with respect to the process, a tubular parison is first generated in a co-extrusion process whereby different polymeric materials are coaxially layered. Subsequently, the parison is inserted in a blow molding fixture, allowing the tube to be longitudinally drawn and radially expanded until the composite film is oriented, the maximum O.D. of the expander member is defined and a desired film thickness is achieved. For example, in forming the parison, PET of a predetermined viscosity may be coextruded with polyethylene where, forming the parison, the polyethylene lines the lumen thereof. When the expander member is formed from the parison in the blow molding operation, the PET layer affords the desired burst strength and limited radial expansion characteristic while the polyethylene layer enhances the ability to bond the resulting balloon to the catheter body.
 The characteristic of lubricity may also be added by coating the exterior of the composite with a suitably lubricious plastic exhibiting high hydrophilic characteristics. Suitable lubricious hydrophilic materials include polycaprolactam polyvinylindol, N-vinylpyrrolidone, various hydrogels, and other hydrophilic lubricious polymeric materials.
 One successful embodiment of the system of the invention utilizes a combination of polyethylene terephthalate (PET) as the tensile layer in combination with a bonding layer of polyethylene. The composite PET/polyethylene balloon was coated on the exterior of the PET with polycaprolactam. By forming a three-layer tubular parison having a layer of plastic with known rupture characteristics, the polyethylene layer may provide the bondability attribute, the PET, the limited radial expansion characteristic and/or the controlled rupture characteristic while polycaprolactam again affords the lubricity.
 Of course, the known rupture or failure characteristics involve the failure by bursting or large scale rupture of the tensile layer rather than the development of small or pin hole leaks in which a small stream of high pressure fluid is released. This minimizes possible damage to surrounding tissue caused by high pressure fluid leakage from the membrane.
 The various features, characteristics and advantages of the invention will become apparent to those skilled in the art from the following detailed description of a preferred embodiment, especially when considered in conjunction with the accompanying drawings in which:
FIG. 1 is a process flow chart illustrative of the present invention;
FIG. 2 is a partial schematic illustration of apparatus for manufacturing parisons in a co-extrusion process;
FIG. 3 is a cross-sectional view of a two-component co-extrusion die useful in forming a two-layer parison;
FIG. 4 illustrates schematically an apparatus for blow molding the parison into a biaxially oriented multilayer expander member;
FIG. 5 shows the expander joined to the distal end of a catheter; and
FIG. 6 depicts an alternative embodiment of the multilayer expander member.
 With reference to FIG. 1, in fabricating the multilayer expander member in accordance with the present invention, the first step in the process is to create a parison which when heated and then drawn and blown creates a balloon or expander member for use on an intravascular catheter. The extruding apparatus is indicated generally by numeral 10 in FIG. 2 and is seen to comprise a motor 12 coupled in driving relationship to a gear box 14 whose output shaft comprises a coarse-pitched archimedian screw 16 rotating within a heated barrel 18. In accordance with known practice, the screw generally has three distinct sections. In the “feed” section 20, directly beneath the feed hopper 22, the screw channel depth is constant and relatively large and serves to convey solid polymer material from the hopper. The depth of the flute in the “compression” section 24 is uniformly tapered and designed to compact the plastic and force it into contact with the barrel 18 to enhance melting. The melting is achieved mainly by a combination of heat conducted from electrical heating elements 26 contained in the barrel and the heat generated by the intense shearing in the molten layer formed between the barrel and the solid material. Numeral 28 identifies the “metering” section of the screw in which the flute depth is constant and relatively small. It controls the output from the extruder in terms of quantity, steadiness and homogeneity. Disposed at the end of the screw 16 is an extruder die 30 which, in the case of the present invention, provides for co-extrusion of at least two different plastics. The first plastic passing through extruder 10 combines with a second plastic exiting a substantially identical extruder shown schematically at 32 to create a concentrically layered tubular parison, the cross-section of which is seen in the view of FIG. 4.
FIG. 3 is a cross-sectional view taken through a two-port co-extrusion die. For example, the output from the metering section 28 of the extruder 10 may be fed into die port A in FIG. 3 while that from the metering section of the screw of extruder 32 feeds port A. The molten plastic flows together to form a layer with the plastic entering port B surrounding the plastic entering port A. As the plastic is made to flow through the die, air is also introduced through the central bore 34 of the die 30 to prevent the collapse of the tubular shaped exudate.
 In accordance with one aspect of the invention, the plastic entering port A, for example, may comprise a polyolefin or PVC while that forced into port B may be a homopolyester, preferably PET, of a predetermined viscosity. With these two constituents, the resulting tubular parison will have the PVC as the inner tubular layer and the PET as its outer layer. The thickness of the individual layers will be determined by the mass flow ratios provided by the respective extruders. The final diameter of the parison is determined by the size of the die exit opening, the total flow of material into ports A and B and the take-away or draw speed.
 The balloon itself is fabricated in a blow molding operation wherein the parison 40 is inserted into the blow mold 42 as shown in FIG. 4 and air or other suitable fluid is introduced through the port 44 at a predetermined pressure. The mold 42 has a cavity 46 corresponding to the desired size of the balloon to be produced.
 After the tubular parison is disposed in the mold, the mold is heated to thereby raise the tubing temperature to a point between the second order transition temperature and the first order transition temperature of the polyester polymer.
 Of course, the inner layer can be caused to adhere to and attach the balloon to the exterior of the tubular catheter body in any desired manner. The material of the inner layer may be such that relatively low melt temperature material can be utilized to achieve a permanent melt bond. Preferably, the exterior of the tubular catheter body is provided with a coating of the same or similar material to that of the inner layer of the multilayer balloon structure such that the materials bonded are substantially identical. This also allows the continuous joint to be made utilizing melt bonding the materials. In this regard, it is desired that the material forming the bonding layer of the multilayer system have a melting temperature sufficiently below that of the material of the tensile layer so that the melt bonding can be achieved without affecting the future physical characteristics of the system.
 As described above, it is desirable that the expander member itself exhibits rather high tensile strength properties. This means exhibiting a burst pressure well in excess of 7 atmospheres while undergoing a radial expansion less than about 3-10 percent. The actual strength, of course, will depend on the relative tensile strength of the material and thickness of the material layer. In addition, these extruded materials are ones not prone to pinhole leaks in the process of the invention in most cases results in a mode of failure, should failure occur, in the form of a rapid rupture which releases the internal pressure over a considerable area in a short time frame so that damage to the vessel is minimized.
 By first drawing the tubular parison and subsequently blow molding same, biaxial orientation takes place whereby the PET layer 56, while remaining flexible, becomes strong as regards the inflation pressure at which the material will burst. When it is desired to bond the finished balloon onto the catheter body as illustrated in FIG. 5, the inner layer 48 of PVC can readily be bonded to an outer PVC tubular body 50 and to an inner tubular body 52, such as by adding adhesive 54 between the outer layer 56 and the inner layer 48. The space between the coaxially disposed tubes allows for injection of a balloon inflation fluid. Balloons produced in accordance with the invention may exhibit a burst pressure well in excess of 7 atmospheres while radially expanding less than about 3-10 percent. While the PVC layer 48 adds little to the burst strength of the composite, it does facilitate the attachment of the balloon to the exterior of the tubular catheter body.
 If it is desired to increase the lubricity of the composite balloon, this may be accomplished by dipping or other coating the multilayer balloon in a suitable hydrophilic material such as polyvinylidol, N-vinylpyrolodone, hydrogels, etc.
 With reference to FIG. 6 and rather than utilizing PET in combination with PVC, a balloon having enhanced properties maybe created by co-extruding a high molecular weight crystalline polyester 60 with a lower molecular weight amorphous polyester 62 in forming the parison. An outer layer of filled polymer 64 adds lubricity. As known in the art, adhesive 66, 68 may be juxtaposed between layers 60, 62 and 64. Following drawing and radial expansion in a blow molding operation, the resulting balloon is found to exhibit high burst strength, low radial expansion and superior bondability as compared to conventional PET single-layer balloons.
 The rupture characteristics of a polymer layer can be modified to increase the rupture rate by adding filler material. The filler materials may be an inert type, such as calcium carbonate, generally in powder form, carbon in fiber form, or an incompatible second phase polymer. Incompatible phase polymer systems afford many advantageous characteristics and are a function of the dispersion between the two phases. Materials which might be candidates for this are polypropylene and selected rubbers, polyester and polypropylene.
 This invention has been described herein in considerable detail in order to comply with the Patent Statutes and to provide those skilled in the art with the information needed to apply the novel principles and to construct and use such specialized components as are required. However, it is to be understood that the invention can be carried out by specifically different equipment and devices, and that various modifications, both as to the equipment details and operating procedures, can be accomplished without departing from the scope of the invention itself.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US2732977 *||Jan 19, 1950||Jan 31, 1956||charpiat|
|US2780378 *||Nov 13, 1953||Feb 5, 1957||Romano Mose||Collapsible container|
|US2915222 *||Mar 22, 1956||Dec 1, 1959||Purinton Bernard S||Flower watering mechanisms|
|US3083877 *||Oct 25, 1960||Apr 2, 1963||Moulded Products Australasia L||Collapsible container with corrugations to facilitate the collapse of its walls|
|US3156383 *||Aug 6, 1962||Nov 10, 1964||Maison Ind Tecnico Chimiche Ne||Expansible single use dispensing container|
|US4197890 *||Dec 18, 1978||Apr 15, 1980||Simko James F||Insulating jacket for bottles|
|US4413989 *||Aug 17, 1981||Nov 8, 1983||Angiomedics Corporation||Expandable occlusion apparatus|
|US4490421 *||Jul 5, 1983||Dec 25, 1984||E. I. Du Pont De Nemours And Company||Balloon and manufacture thereof|
|US4799717 *||Sep 2, 1987||Jan 24, 1989||Mace Corporation||Torque lock fitting arrangement|
|US4886194 *||Mar 25, 1988||Dec 12, 1989||Schiemann Dr Wolfram||Discharge tube|
|US4976697 *||Oct 26, 1989||Dec 11, 1990||Becton, Dickinson And Company||Catheter obturator with automatic feed and control|
|US5041125 *||Mar 26, 1990||Aug 20, 1991||Cordis Corporation||Balloon catheter|
|US5195969 *||Apr 26, 1991||Mar 23, 1993||Boston Scientific Corporation||Co-extruded medical balloons and catheter using such balloons|
|US5242422 *||Nov 29, 1991||Sep 7, 1993||Professional Medical Products, Inc.||One piece molded syringe with tethered cap|
|US5248071 *||Jun 26, 1991||Sep 28, 1993||Ray Cecil D||Re-sealable nozzle and cap assembly|
|US5248305 *||Aug 24, 1992||Sep 28, 1993||Cordis Corporation||Extruded tubing and catheters having helical liquid crystal fibrils|
|US5288529 *||Jun 18, 1990||Feb 22, 1994||Foster-Miller Inc.||Liquid crystal polymer film|
|US5589236 *||Mar 24, 1994||Dec 31, 1996||Superex Polymer Inc.||Coextrusion of liquid crystal polymers and thermoplastic polymers|
|US5755690 *||Oct 21, 1994||May 26, 1998||C. R. Bard||Multiple layer high strength balloon for dilatation catheter|
|US5797877 *||May 24, 1996||Aug 25, 1998||Boston Scientific Corporation||Medical device balloons containing thermoplastic elastomers|
|US5833657 *||May 3, 1996||Nov 10, 1998||Ethicon, Inc.||Single-walled balloon catheter with non-linear compliance characteristic|
|US5879369 *||Oct 10, 1996||Mar 9, 1999||Terumo Kabushiki Kaisha||Catheter balloon and balloon catheter|
|US5908406 *||Jan 29, 1997||Jun 1, 1999||E. I. Du Pont De Nemours And Company||Dilatation catheter balloons with improved puncture resistance|
|US5961765 *||Sep 24, 1997||Oct 5, 1999||Schneider (Europe) A. G.||Method of making a catheter|
|US6004289 *||Mar 28, 1997||Dec 21, 1999||Medtronic Ave, Inc.||Multiple layer high strength balloon for dilatation catheter|
|US6027477 *||Apr 2, 1998||Feb 22, 2000||Schneider (Europe) A.G.||Catheter with multilayer tube|
|US6059751 *||Feb 5, 1999||May 9, 2000||E. I. Du Pont De Nemours And Company||Dilatation catheter balloons with improved puncture resistance|
|US6086556 *||Aug 4, 1998||Jul 11, 2000||Boston Scientific Corporation||Medical device balloons containing thermoplastic elastomers|
|US6132824 *||Aug 6, 1997||Oct 17, 2000||Schneider (Usa) Inc.||Multilayer catheter balloon|
|US6136258 *||Apr 24, 1995||Oct 24, 2000||Boston Scientific Corporation||Method of forming a co-extruded balloon for medical purposes|
|US6270522 *||Dec 21, 1999||Aug 7, 2001||Advanced Cardiovascular Systems, Inc.||High pressure catheter balloon|
|US6319228 *||Apr 25, 1997||Nov 20, 2001||Schneider (Europe) A.G.||Multilayer interventional catheter|
|US6336936 *||Jun 13, 2001||Jan 8, 2002||Advanced Cardiovascular Systems, Inc||High pressure catheter balloon|
|US6464683 *||Oct 24, 2000||Oct 15, 2002||Schneider (Usa) Inc.||Trilayer, extruded medical tubing and medical devices incorporating such tubbing|
|US6471673 *||May 24, 1999||Oct 29, 2002||Schneider (Europe) A.G.||Catheter with multilayer tube|
|US6482348 *||Apr 3, 2000||Nov 19, 2002||Boston Scientific Corporation||Method of forming a co-extruded balloon for medical purposes|
|US6485457 *||Sep 27, 2000||Nov 26, 2002||Terumo Kabushiki Kaisha||Catheter|
|US6488655 *||Dec 15, 2000||Dec 3, 2002||Advanced Cardiovascular Systems, Inc.||Polymer jacket with adhesive inner layer|
|US6659977 *||Oct 15, 2001||Dec 9, 2003||Schneider (Europe) A.G.||Multilayer interventional catheter|
|US20040207127 *||May 5, 2004||Oct 21, 2004||Schneider (Usa) Inc., A Corporation||Method of making multilayer angioplasty catheter balloon|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7828766||Dec 20, 2005||Nov 9, 2010||Advanced Cardiovascular Systems, Inc.||Non-compliant multilayered balloon for a catheter|
|US7906066||Jun 30, 2006||Mar 15, 2011||Abbott Cardiovascular Systems, Inc.||Method of making a balloon catheter shaft having high strength and flexibility|
|US8052638||Nov 8, 2011||Abbott Cardiovascular Systems, Inc.||Robust multi-layer balloon|
|US8070719||Nov 26, 2008||Dec 6, 2011||Abbott Cardiovascular Systems, Inc.||Low compliant catheter tubing|
|US8382738||Jun 15, 2007||Feb 26, 2013||Abbott Cardiovascular Systems, Inc.||Balloon catheter tapered shaft having high strength and flexibility and method of making same|
|US8388575||Apr 16, 2012||Mar 5, 2013||Abbott Cardiovascular Systems Inc.||Non-compliant multilayered balloon for a catheter|
|US8388602||Mar 5, 2013||Abbott Cardiovascular Systems Inc.||Balloon catheter shaft having high strength and flexibility|
|US8394055||Mar 12, 2013||Abbott Cardiovascular Systems Inc.||Non-compliant multilayered balloon for a catheter|
|US8403885||Dec 17, 2007||Mar 26, 2013||Abbott Cardiovascular Systems Inc.||Catheter having transitioning shaft segments|
|US8535596||Feb 15, 2012||Sep 17, 2013||Abbott Cardiovascular Systems, Inc.||Non-compliant multilayered balloon for a catheter|
|US8613722||Sep 22, 2011||Dec 24, 2013||Abbott Cardiovascular Systems, Inc.||Robust multi-layer balloon|
|US8657782||Jul 31, 2012||Feb 25, 2014||Abbott Cardiovascular Systems, Inc.||Catheter having transitioning shaft segments|
|US8721624||Feb 25, 2013||May 13, 2014||Abbott Cardiovascular Systems Inc.||Balloon catheter shaft having high strength and flexibility|
|US8771332||May 29, 2008||Jul 8, 2014||Boston Scientific Scimed, Inc.||Multi-layer balloon design for use in combination with catheter assemblies, and methods of making the same|
|US9056190||Feb 25, 2013||Jun 16, 2015||Abbott Cardiovascular Systems Inc.||Balloon catheter tapered shaft having high strength and flexibility and method of making same|
|US9095689||Feb 25, 2013||Aug 4, 2015||Abbott Cardiovascular Systems Inc.||Non-compliant multilayered balloon for a catheter|
|US20040207127 *||May 5, 2004||Oct 21, 2004||Schneider (Usa) Inc., A Corporation||Method of making multilayer angioplasty catheter balloon|
|WO2009146280A1 *||May 20, 2009||Dec 3, 2009||Boston Scientific Scimed, Inc.||Multi-layer balloon design for use in combination with catheter assemblies, and methods of making the same|
|International Classification||A61L29/00, B01J13/02, A61M29/02, A61F2/958, A61L29/04, A61M25/00, A61L29/12, A61L29/06, B29C49/22, B29C49/04|
|Cooperative Classification||A61M25/1029, A61M2025/1075, A61M25/1034, Y10T428/1393, B29C49/22, A61L29/041, A61M2025/1031, B29K2023/06, A61M25/0009, Y10T428/1397, B29L2031/7542, B29C49/04, A61L29/06, A61M25/0045, Y10T428/139, A61L29/126, B29K2023/083, B29K2067/00, Y10T428/1334|
|European Classification||A61M25/10G1, A61L29/04B, A61L29/12D, A61L29/06, A61M25/00S1, B29C49/22, A61M25/00G|
|Oct 30, 2006||AS||Assignment|
Owner name: SCIMED LIFE SYSTEMS, INC., MINNESOTA
Free format text: MERGER;ASSIGNOR:BOSTON SCIENTIFIC SCIMED, INC.;REEL/FRAME:018454/0834
Effective date: 20050101
Owner name: BOSTON SCIENTIFIC SCIMED, INC., MINNESOTA
Free format text: CHANGE OF NAME;ASSIGNOR:SCHNEIDER (USA) INC.;REEL/FRAME:018454/0858
Effective date: 19990427
Owner name: BOSTON SCIENTIFIC SCIMED, INC., MINNESOTA
Free format text: CHANGE OF NAME;ASSIGNOR:SCIMED LIFE SYSTEMS, INC.;REEL/FRAME:018454/0866
Effective date: 20050101