|Publication number||USRE36628 E|
|Application number||US 08/950,602|
|Publication date||Mar 28, 2000|
|Filing date||Oct 16, 1997|
|Priority date||Jan 7, 1987|
|Publication number||08950602, 950602, US RE36628 E, US RE36628E, US-E-RE36628, USRE36628 E, USRE36628E|
|Inventors||Kyuta Sagae, Yoshiaki Sugiyama|
|Original Assignee||Terumo Kabushiki Kaisha|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (29), Non-Patent Citations (8), Referenced by (68), Classifications (13), Legal Events (2)|
|External Links: USPTO, USPTO Assignment, Espacenet|
.[.This application is a division of application Ser. No. 07/657,895, filed Feb. 19, 1991, now abandoned, which is a continuation of Ser. No. 07/381,391 filed Jul. 5, 1989, now abandoned..]. .Iadd.This application is a continuation of application Ser. No. 08/671,972, filed Jun. 28, 1996, now abandoned, which is a continuation of application Ser. No. 08/357,570, filed Dec. 15, 1994 now abandoned, which is a Reissue of U.S. Pat. No. 5,171,383, issued Dec. 15, 1992, which is a divisional of application Ser. No. 07/657,895, filed Feb. 19, 1991, abandoned, which is a continuation of application Ser. No. 07/381,391, filed Jul. 5, 1989, now abandoned. .Iaddend.
The present invention relates to a catheter guide wire for guiding a clinical or testing catheter to a predetermined portion of a body cavity such as a blood vessel, a digestive tract, and a windpipe and holding it therein, and a method of manufacturing the same.
When a catheter is to be guided to a branching peripheral portion of a blood vessel or the like, first, a guide wire must be guided to a target portion. In this case, since a target portion is generally thin and thus tends to be easily damaged, the distal end portion of the guide wire must be flexible so that it will not damage a blood vessel wall, will follow the shape of the blood vessel well even if the blood vessel is curved, and can be inserted in a complex branching blood vessel. Meanwhile, the proximal end portion of the guide wire must have torque transmitting performance so that a manual operation performed at the proximal end portion is transmitted to the distal end portion. Thus, the proximal end portion of the guide wire must have comparatively high rigidity.
According to a conventional catheter guide wire having the above characteristics, a coil guide wire is made of a stainless steel wire or a piano wire, or a guide wire is made of a plastic monofilament. In each of these guide wires, its sectional area is decreased from its proximal to distal end portion, and the guide wire forms a main portion having relatively high rigidity and a relatively flexible distal end portion.
However, plastic deformation can easily occur in these conventional guide wires, and some manual operation can kink the guide wires. A kinked portion becomes an obstacle during introduction of a catheter, thus rendering smooth introduction operation of a catheter impossible as well as greatly degrading its torque transmitting performance.
A catheter guide wire free from such kinking deformation uses a very elastic alloy (e.g., Ni-Ti alloy) as a core member (see Japanese Patent Disclosure (Kokai) No. 60-63066).
A guide wire using a very elastic alloy is flexible and can restore its original shape after it is deformed to a considerable degree (strain of about 8%). Therefore, such a guide wire cannot be easily broken during operation and will not easily attain a bending tendency. However, such guide wire has a high elasticity at its distal end portion and is thus infavorable in terms of flexibility. Then the diameter of its proximal end portion is 0.5 mm or less, the rigidity is insufficient and the torque transmitting performance is poor.
The present invention has been made in view of the above situation and has as its object to provide a catheter guide wire wherein its distal end portion is very flexible, buckling deformation is difficult to occur, and its proximal end portion is very rigid, thus having a good torque transmitting performance to the distal end portion, and a method of manufacturing the same.
In order to solve the above problems, according to the present invention, a wire member made of an elastic alloy, and preferably a very elastic alloy, is used as a core member of a catheter guide wire and subjected to a heat treatment by changing the treatment conditions along its longitudinal direction, so that the rigidity at its proximal end portion becomes comparatively high, the flexibility at its distal end portion is increased, and kinking deformation will not easily occur in its distal end portion.
More specifically, according to the present invention, there is provided a catheter guide wire having leading and trailing end sides, characterized in that the guide wire comprises a wire member made of an elastic alloy member, at least the leading end side thereof has an outer diameter equal to or smaller than a minimum inner diameter of a catheter, and the wire member is subjected to a heat treatment so that its flexibility is sequentially increased from a proximal to distal end portion of the leading end side thereof.
Note that the catheter guide wire can be fabricated by using as a core member a wire member made of an elastic alloy member subjected to the heat treatment described above and forming a cover layer of a thermoplastic resin on the core member.
The core member preferably uses a very elastic alloy such as an Ni-Ti alloy, a Cu-Zn-Al alloy, a Cu-Al-Ni alloy, and an Fe-Mn alloy. The core member is preferably tapered such that a diameter at its distal end portion is smaller than that at its proximal end portion. A contrast medium such as a tungsten powder can be added to the thermoplastic resin layer.
A flexible coil spring having an outer diameter equal to or smaller than a minimum inner diameter of the catheter can be mounted to surround at least the distal end portion of the wire member.
In this case, the coil spring is preferably made of a material having a high X-ray impermeability in order to allow an X-ray photographing to be easily confirmed. Therefore, the presence of the coil spring is advantageous in giving a sufficient thickness in an X-ray image without badly affecting the flexibility of the guide wire.
As a result, the coil spring is made of a material selected from a group consisting of stainless steel, platinum, a platinum alloy and a palladium alloy, and preferably has a thickness of 0.01 to 0.15 mm, more preferably 0.05 to 0.1 mm.
Furthermore, according to the present invention, there is provided a method of manufacturing a catheter guide wire fabricated by using an elastic alloy wire as a base material, characterized in that a leading end side of the base material is divided into a plurality of areas, and a heat treatment is performed by changing the temperatures and time in units of the areas so that the flexibility of the base material is sequentially increased from the proximal to distal end portion of the leading end side.
In a conventional catheter guide wire, a diameter at a proximal end portion of a wire member made of an elastic alloy or a very elastic alloy is merely increased, and a diameter at its distal end portion is relatively decreased, thereby making the proximal end portion rigid and the distal end portion flexible. Unlike such a conventional catheter guide wire, according to the present invention, a wire member is subjected to a heat treatment by sequentially changing the confunction along its longitudinal direction. As a result, the physical characteristics of the wire member can be set in an ideal state as a catheter guide wire.
FIG. 1 is a sectional view of a catheter guide wire according to an embodiment of the present invention;
FIG. 2 is a graph of strain-stress curves of the core member of the guide wire according to the embodiment of the present invention; and
FIGS. 3 and 4 respectively represent a sectional view of a catheter guide wire on which a coil spring is mounted according to another embodiment of the present invention.
Preferred embodiments of the present invention will be described with reference to the accompanying drawings.
FIG. 1 is a sectional view of a catheter guide wire taken along the longitudinal direction according to an embodiment of the present invention. Referring to FIG. 1, reference numeral 1 denotes a core member; and 2, a thermoplastic resin layer entirely covering core member 1.
Core member 1 is a wire member made of an elastic alloy wire such as a piano wire, and preferably a very elastic alloy such as an Ni-Ti alloy. Core member 1 can have a uniform diameter of 0.2 to 0.4 mm, or can be tapered toward its distal end such that the diameter at its proximal end portion is 0.2 to 0.4 mm and the diameter at its distal end portion is 0.01 to 0.1 mm. In this specification, a very elastic alloy is defined as an alloy whose recoverable elastic strain is as large as several % to more than ten % and whose stress level does not exceed a predetermined value even if the strain is increased. The very elastic alloy generally comprises an Ni-Ti, Cu-Zn-Al, Cu-Al-Ni, or Fe-Mn alloy. If an Ni-Ti alloy is employed, it preferably contains 49 to 58 atm. % of Ni and a balance of Ti, and more preferably 49 to 51 atm. % of Ni and a balance of Ti. If a Cu-Zn-Al alloy is employed, it preferably contains 38.5 to 41.5 wt. % of Zn, 1 to 10 wt. % of ADP, and a balance of Cu. If a Cu-Al-Ni alloy is employed, it preferably contains 14 to 14.5 wt. % of Al, 3 to 4.5 wt. % of Ni, and a balance of Cu. If an Fe-Mn alloy is employed, it preferably contains 28 to 32 wt. % of Mn, 6 wt. % of Si, and a balance of Fe. A heat treatment is performed by changing the treatment conditions. As a result, the guide wire can have the following physical characteristics in its areas (1) to (III) as shown in FIG. 1.
(1) Proximal end portion (I)
When the guide wire is guided from, e.g., a straight great blood vessel (e.g., a descending aorta) to an arteriole (e.g., a coronary artery), proximal end a comparatively small number of bent portions. Proximal and portion (I) has a comparatively high rigidity and is difficult to deform. Therefore, forward/backward movement and rotation externally applied to the catheter can be easily transmitted to the distal end portion (II--III) through a blood vessel retaining an introducer (not shown).
(2) Intermediate portion (II)
Intermediate portion (II) has an elasticity so that it can easily follow a blood vessel curve of a comparatively large curve and can return to its initial shape when deformation caused by the curve is removed. Although it is flexible, intermediate portion (II) hardly attains a bending tendency and is difficult to break.
(3) Distal end portion (III)
When distal end portion (III) is inserted in a small, curved blood vessel, it can easily follow the blood vessel shape due to its flexibility, and thus will not damage the blood vessel wall. When a blood vessel has phatologic factor such as arteriosclerosis, the flexibility of distal end portion (III) is important.
Thermoplastic resin layer 2 is provided as needed in order to protect the inner surface of the blood vessel, to prevent formation of thrombus on an outer surface of the guide wire during operation of the guide wire, and not to form a difference in outer diameter between the proxital end portion and the distal end portion. For example, saturated aliphatic polyether urethane is used to form layer 2. A contrast medium can be mixed in the thermoplastic resin in advance in order to increase the contrast of the guide wire through X-ray photographing. For example, 40 to 600 parts by weight (with respect to 100 parts by weight of thermoplastic resin) of a tungsten powder can be mixed as the contrast medium. Note that saturated aliphatic polyether polyurethane is favorable for compounding of tungsten.
FIG. 2 shows the physical characteristics (strain-stress curve) at the respective portions of the core member of the present invention after a heat treatment. A heat treatment can be performed in an atmosphere of an inert gas (Ar or He), vacuum (×10-2 Torr or less) or outer atmosphere. Although a heat treatment can be performed in an outer atmosphere, it is preferably performed in a vacuum in view of embrittlement of the material, and more preferably in an inert gas. The values in FIG. 2 are obtained by cutting the core member sample into 70-mm long pieces starting from its distal end and subjecting the respective samples to a tension test.
Core member: Ni-Ti alloy wire (diameter: 0.4 mm) (49 atm. % of Ni and a balance of Ti)
Heat treatment conditions:
______________________________________ TensionArea of TestGuide Wire Heat Treatment Conditions Sample No.______________________________________Distal end About 2 hrs. at 400 to 500° C. (1) (2)portion (III) and about 24 hrs. at 200° C. (in outer atmosphere)Intermediate About 2 hrs. at 400 to 500° C. (3) (4) (5)portion (II) (in outer atmosphere)Proximal end No heat treatment after (6)portion (I) cold rolling______________________________________
The physical characteristics at the respective portions of core member 1 are not limited to those shown in FIG. 2 and can be arbitrarily adjusted and selected in accordance with specific applications.
FIG. 3 is a partial sectional view of a catheter guide wire according to another embodiment of the present invention. Thermoplastic resin layer 2 is formed on the entire surface of core member 1 in the same manner as in FIG. 1, and coil spring 3 having a thickness of 0.08 mm is mounted on an outer surface of resin layer 2 excluding its leading and trailing end faces. Note that coil spring 3 may be provided at only the distal end portion of the guide wire. The outer diameter of the guide wire may be conveniently selected to conform with the inner diameter of a blood vessel to be inserted. Generally, however, the outer diameter of the guide wire may be selected within a range of from 0.2 to 2.0 mm.
When coil spring 3 is applied on resin layer 2 in this manner, the physical characteristics of the guide wire are as flexible at its distal end portion as shown in FIG. 1 and highly resistive to buckling deformation due to the high flexibility of the coil spring 3, relatively high in rigidity at its proximal end portion and excellent in X-ray photographing.
Coil spring 3 can be provided to directly surround core member 1 without intervening thermoplastic resin layer 2.
FIG. 4 shows an example of such a structure of the guide wire, wherein the coil spring 3 is directly wound around the outer wall of core member 1, with its distal and proximal end portions being fixed to core member 1 through a soldering material 4 made for example of Sn-Ag (96:4) alloy.
As described above, according to the catheter guide wire of the present invention, a wire member made of an elastic alloy is used as a core member and subjected to a heat treatment by sequentially changing the treatment conditions along its longitudinal direction. As a result, the proximal end portion of the guide wire has predetermined rigidity required in accordance with its application, and its distal end portion has predetermined flexibility.
The guide wire as proposed by this invention is useful for guiding a clinical or testing catheter to a predetermined portion of a body cavity such as blood vessel, a digestive tract and a windpipe, and holding it therein for a period of time.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3521620 *||Oct 30, 1967||Jul 28, 1970||Cook William A||Vascular coil spring guide with bendable tip|
|US3789841 *||Sep 15, 1971||Feb 5, 1974||Becton Dickinson Co||Disposable guide wire|
|US3906938 *||Sep 3, 1974||Sep 23, 1975||Lake Region Manufacturing Comp||Coil spring wire guide|
|US4037324 *||May 21, 1973||Jul 26, 1977||The University Of Iowa Research Foundation||Method and system for orthodontic moving of teeth|
|US4144057 *||Aug 25, 1977||Mar 13, 1979||Bbc Brown, Boveri & Company, Limited||Shape memory alloys|
|US4484955 *||Dec 12, 1983||Nov 27, 1984||Hochstein Peter A||Shape memory material and method of treating same|
|US4654092 *||Aug 5, 1985||Mar 31, 1987||Raychem Corporation||Nickel-titanium-base shape-memory alloy composite structure|
|US4665906 *||May 21, 1986||May 19, 1987||Raychem Corporation||Medical devices incorporating sim alloy elements|
|US4748986 *||Jan 29, 1987||Jun 7, 1988||Advanced Cardiovascular Systems, Inc.||Floppy guide wire with opaque tip|
|US4813434 *||Mar 31, 1988||Mar 21, 1989||Medtronic Versaflex, Inc.||Steerable guidewire with deflectable tip|
|US4925445 *||Feb 9, 1989||May 15, 1990||Fuji Terumo Co., Ltd.||Guide wire for catheter|
|US4935068 *||Jan 23, 1989||Jun 19, 1990||Raychem Corporation||Method of treating a sample of an alloy|
|US4943326 *||Oct 20, 1988||Jul 24, 1990||The Furukawa Electric Co., Ltd.||Ornament and method of manufacturing the same|
|US4984581 *||Oct 12, 1988||Jan 15, 1991||Flexmedics Corporation||Flexible guide having two-way shape memory alloy|
|US5069226 *||Apr 27, 1990||Dec 3, 1991||Tokin Corporation||Catheter guidewire with pseudo elastic shape memory alloy|
|US5190546 *||Apr 9, 1991||Mar 2, 1993||Raychem Corporation||Medical devices incorporating SIM alloy elements|
|US5230348 *||Oct 11, 1991||Jul 27, 1993||Nippon Seisen Co., Ltd.||Guide wire for a catheter|
|US5238004 *||Sep 30, 1992||Aug 24, 1993||Boston Scientific Corporation||High elongation linear elastic guidewire|
|US5341818 *||Dec 22, 1992||Aug 30, 1994||Advanced Cardiovascular Systems, Inc.||Guidewire with superelastic distal portion|
|US5637089 *||Feb 12, 1996||Jun 10, 1997||Advanced Cardiovascular Systems, Inc.||Superelastic guiding member|
|EP0013604A1 *||Jan 4, 1980||Jul 23, 1980||Medtronic, Inc.||Flexible tip stiffening stylet for body implantable lead|
|EP0141006A1 *||Jan 27, 1984||May 15, 1985||Terumo Kabushiki Kaisha||Guide wire for catheter|
|EP0161066A1 *||Apr 3, 1985||Nov 13, 1985||RAYCHEM CORPORATION (a Delaware corporation)||Nickel/titanium-base alloys|
|JPS5948643A *||Title not available|
|JPS6063066A *||Title not available|
|JPS59219443A *||Title not available|
|JPS60138547A *||Title not available|
|JPS61106173A *||Title not available|
|WO1985001444A1 *||Oct 4, 1984||Apr 11, 1985||Maerz Peter||Guiding mandrel for catheter and similar instruments and manufacturing process thereof|
|1||*||Derwint Abs C85 008891 (of Japan 59 125,447), 1985.|
|2||*||Derwint Abs C85 008892 (of Japan 59 125,448), 1985.|
|3||Derwint Abs C85-008891 (of Japan 59-125,447), 1985.|
|4||Derwint Abs C85-008892 (of Japan 59-125,448), 1985.|
|5||G. Andreasen et al., "Laboratory and clinical analysis of nitinol wire," A. J. Orthod., vol. 73, No. 2, pp. 142-151 (1978).|
|6||*||G. Andreasen et al., Laboratory and clinical analysis of nitinol wire, A. J. Orthod., vol. 73, No. 2, pp. 142 151 (1978).|
|7||K. Watanabe, "Studies on New Superelastic NiTi Orthodontic Wire," vol. 23, No. 61 (1982); English abstract only.|
|8||*||K. Watanabe, Studies on New Superelastic NiTi Orthodontic Wire, vol. 23, No. 61 (1982); English abstract only.|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US6280539 *||Feb 7, 2000||Aug 28, 2001||Advance Cardiovascular Systems, Inc.||Superelastic guiding member|
|US6582536 *||Apr 12, 2001||Jun 24, 2003||Biotran Corporation Inc.||Process for producing steerable sheath catheters|
|US6790170||Nov 7, 2001||Sep 14, 2004||Theragenics Corporation||Radioactive source wire and dual lumen catheter system for brachytherapy|
|US7244319||Nov 11, 2002||Jul 17, 2007||Abbott Cardiovascular Systems Inc.||Superelastic guiding member|
|US7455737 *||Aug 25, 2003||Nov 25, 2008||Boston Scientific Scimed, Inc.||Selective treatment of linear elastic materials to produce localized areas of superelasticity|
|US7637875||Sep 26, 2007||Dec 29, 2009||Terumo Kabushiki Kaisha||Guide wire|
|US7641622||Oct 4, 2007||Jan 5, 2010||Terumo Kabushiki Kaisha||Guide wire|
|US7665212||Feb 23, 2005||Feb 23, 2010||Ultradent Products, Inc.||Methods for manufacturing endodontic instruments|
|US7743505||Feb 23, 2005||Jun 29, 2010||Ultradent Products, Inc.||Methods for manufacturing endodontic instruments from powdered metals|
|US7744545||Sep 26, 2007||Jun 29, 2010||Terumo Kabushiki Kaisha||Guide wire|
|US7753859||May 7, 2008||Jul 13, 2010||Terumo Kabushiki Kaisha||Guide wire|
|US7762962||Jan 11, 2008||Jul 27, 2010||Terumo Kabushiki Kaisha||Intermediate member, and a medical device and guide wire including such an intermediate member|
|US7780611||May 1, 2003||Aug 24, 2010||Boston Scientific Scimed, Inc.||Medical instrument with controlled torque transmission|
|US7896820||Dec 21, 2007||Mar 1, 2011||Terumo Kabushiki Kaisha||Guide wire|
|US7918011||Oct 10, 2007||Apr 5, 2011||Abbott Cardiovascular Systems, Inc.||Method for providing radiopaque nitinol alloys for medical devices|
|US7938843||Jun 9, 2003||May 10, 2011||Abbott Cardiovascular Systems Inc.||Devices configured from heat shaped, strain hardened nickel-titanium|
|US7942892||May 1, 2003||May 17, 2011||Abbott Cardiovascular Systems Inc.||Radiopaque nitinol embolic protection frame|
|US7976648||Nov 2, 2000||Jul 12, 2011||Abbott Cardiovascular Systems Inc.||Heat treatment for cold worked nitinol to impart a shape setting capability without eventually developing stress-induced martensite|
|US8002909 *||Oct 5, 2009||Aug 23, 2011||Boston Scientific Scimed, Inc.||Medical devices|
|US8128580||Mar 28, 2008||Mar 6, 2012||Terumo Kabushiki Kaisha||Guide wire|
|US8172774||Mar 20, 2008||May 8, 2012||Terumo Kabushiki Kaisha||Guide wire|
|US8206837||Sep 27, 2007||Jun 26, 2012||Terumo Kabushiki Kaisha||Interventional medical device|
|US8292829||Jul 13, 2010||Oct 23, 2012||Boston Scientific Scimed, Inc.||Medical instrument with controlled torque transmission|
|US8485992 *||Jul 20, 2010||Jul 16, 2013||Boston Scientific Scimed, Inc.||Medical device having segmented construction|
|US8728010 *||Aug 24, 2006||May 20, 2014||Boston Scientific Scimed, Inc.||Elongate medical device including deformable distal end|
|US8758268||Feb 8, 2008||Jun 24, 2014||C. R. Bard, Inc.||Shape memory medical device and methods of use|
|US8845552||Sep 14, 2012||Sep 30, 2014||Boston Scientific Scimed, Inc.||Medical instrument with controlled torque transmission|
|US8900216 *||Nov 18, 2011||Dec 2, 2014||Johan Willem Pieter Marsman||Facilitation of antegrade insertion of a guidewire into the superficial femoral artery|
|US9387308 *||Mar 5, 2010||Jul 12, 2016||Cardioguidance Biomedical, Llc||Guidewire with adjustable stiffness|
|US9387309 *||Dec 19, 2012||Jul 12, 2016||Cardioguidance Biomedical, Llc||Guidewire with adjustable stiffness|
|US9498603 *||Dec 11, 2012||Nov 22, 2016||Cardioguidance Biomedical, Llc||Guidewire with adjustable stiffness|
|US20030127158 *||Nov 11, 2002||Jul 10, 2003||Abrams Robert M.||Superelastic guiding member|
|US20030145915 *||Feb 28, 2003||Aug 7, 2003||Jin Shimada||Process for producing steerable sheath catheters|
|US20030199920 *||Jun 9, 2003||Oct 23, 2003||Boylan John F.||Devices configured from heat shaped, strain hardened nickel-titanium|
|US20040167438 *||Feb 26, 2003||Aug 26, 2004||Sharrow James S.||Reinforced medical device|
|US20040193207 *||Mar 26, 2003||Sep 30, 2004||Scimed Life Systems, Inc.||Method for manufacturing medical devices from linear elastic materials while maintaining linear elastic properties|
|US20040220499 *||May 1, 2003||Nov 4, 2004||Scimed Life Systems, Inc.||Medical instrument with controlled torque transmission|
|US20040220608 *||May 1, 2003||Nov 4, 2004||D'aquanni Peter||Radiopaque nitinol embolic protection frame|
|US20040225175 *||Jun 3, 2004||Nov 11, 2004||Moody Michael R.||Radioactive source wire and dual lumen catheter system brachytherapy|
|US20050049690 *||Aug 25, 2003||Mar 3, 2005||Scimed Life Systems, Inc.||Selective treatment of linear elastic materials to produce localized areas of superelasticity|
|US20060185169 *||Feb 23, 2005||Aug 24, 2006||Paul Lewis||Methods for manufacturing endodontic instruments|
|US20060212068 *||May 22, 2006||Sep 21, 2006||Advanced Cardiovascular Systems, Inc.||Embolic protection device with an elongated superelastic radiopaque core member|
|US20070149037 *||Dec 26, 2006||Jun 28, 2007||Terumo Kabushiki Kaisha||Guide wire|
|US20070239259 *||Mar 19, 2007||Oct 11, 2007||Advanced Cardiovascular Systems Inc.||Nitinol alloy design and composition for medical devices|
|US20070249965 *||Apr 10, 2007||Oct 25, 2007||Advanced Cardiovascular System, Inc.||Superelastic guiding member|
|US20080027532 *||Oct 10, 2007||Jan 31, 2008||Abbott Cardiovascular Systems Inc.||Radiopaque nitinol alloys for medical devices|
|US20080058859 *||Aug 31, 2007||Mar 6, 2008||Chanduszko Andrzej J||Medical Devices Utilizing Modified Shape Memory Alloy|
|US20080077049 *||Aug 24, 2006||Mar 27, 2008||Boston Scientific Scimed, Inc.||Elongate medical device including deformable distal end|
|US20080119762 *||Sep 21, 2007||May 22, 2008||Tateishi Tadasu||Guide wire|
|US20080154152 *||Dec 21, 2007||Jun 26, 2008||Hideo Satou||Guide wire|
|US20080161726 *||Sep 26, 2007||Jul 3, 2008||Yutaka Itou||Guide wire|
|US20080161727 *||Sep 26, 2007||Jul 3, 2008||Youki Aimi||Guide wire|
|US20080171217 *||Sep 27, 2007||Jul 17, 2008||Katsuro Mishima||Brazing Material, Interventional Medical Device, and Joined Assembly|
|US20080171952 *||Jan 11, 2008||Jul 17, 2008||Katsuro Mishima||Intermediate member, and a medical device and guide wire including such an intermediate member|
|US20080194992 *||Oct 4, 2007||Aug 14, 2008||Terumo Kabushiki Kaisha||Guide wire|
|US20080194994 *||Feb 8, 2008||Aug 14, 2008||C.R. Bard, Inc.||Shape memory medical device and methods of use|
|US20080234606 *||Mar 20, 2008||Sep 25, 2008||Terumo Kabushiki Kaisha||Guide Wire|
|US20080281230 *||May 7, 2008||Nov 13, 2008||Terumo Kabushiki Kaisha||Guide Wire|
|US20090157050 *||Mar 28, 2008||Jun 18, 2009||Terumo Kabushiki Kaisha||Guide wire|
|US20090248130 *||Feb 11, 2009||Oct 1, 2009||Abbott Cardiovascular Systems, Inc.||Nitinol alloy design and composition for vascular stents|
|US20090292225 *||May 21, 2008||Nov 26, 2009||Boston Scientific Scimed, Inc.||Medical device including a braid for crossing an occlusion in a vessel|
|US20100114304 *||Oct 5, 2009||May 6, 2010||Scimed Life Systems||Medical Devices|
|US20100249655 *||Mar 29, 2010||Sep 30, 2010||C. R. Bard, Inc.||Tip-Shapeable Guidewire|
|US20100286566 *||Jul 20, 2010||Nov 11, 2010||Boston Scientific Scimed, Inc.||Medical device having segmented construction|
|US20100305475 *||Mar 5, 2010||Dec 2, 2010||Hinchliffe Peter W J||Guidewire with adjustable stiffness|
|US20120065591 *||Nov 18, 2011||Mar 15, 2012||Johan Willem Pieter Marsman||Facilitation Of Antegrade Insertion Of A Guidewire Into The Superficial Femoral Artery|
|US20130131643 *||Dec 11, 2012||May 23, 2013||Cardioguidance Biomedical, Llc||Guidewire with adjustable stiffness|
|US20130131644 *||Dec 19, 2012||May 23, 2013||Cardioguidance Biomedical, Llc||Guidewire with adjustable stiffness|
|U.S. Classification||148/537, 148/676, 148/564, 148/563, 148/902, 600/585, 604/530, 604/525|
|Cooperative Classification||A61M25/09, A61M2025/09083, A61M2025/09141|
|Jun 5, 2000||FPAY||Fee payment|
Year of fee payment: 8
|May 12, 2004||FPAY||Fee payment|
Year of fee payment: 12