CA2515145A1 - Elongate medical device with distal cap - Google Patents

Elongate medical device with distal cap Download PDF

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Publication number
CA2515145A1
CA2515145A1 CA002515145A CA2515145A CA2515145A1 CA 2515145 A1 CA2515145 A1 CA 2515145A1 CA 002515145 A CA002515145 A CA 002515145A CA 2515145 A CA2515145 A CA 2515145A CA 2515145 A1 CA2515145 A1 CA 2515145A1
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CA
Canada
Prior art keywords
distal
distal end
core wire
cap
medical device
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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.)
Abandoned
Application number
CA002515145A
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French (fr)
Inventor
Brian R. Reynolds
Peter Skujins
Dave Johnson
Alan D. Eskuri
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Boston Scientific Ltd Barbados
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Individual
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Filing date
Publication date
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Publication of CA2515145A1 publication Critical patent/CA2515145A1/en
Abandoned legal-status Critical Current

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Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M25/00Catheters; Hollow probes
    • A61M25/01Introducing, guiding, advancing, emplacing or holding catheters
    • A61M25/09Guide wires
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M25/00Catheters; Hollow probes
    • A61M25/01Introducing, guiding, advancing, emplacing or holding catheters
    • A61M25/09Guide wires
    • A61M2025/09175Guide wires having specific characteristics at the distal tip

Abstract

Elongate medical devices such as guidewires can be formed from a core wire and a preformed distal cap that is configured to fit over a distal end of the core wire. The distal cap can be attached using a variety of techniques. In particular, the distal cap can be attached to the core wire using laser welding.

Description

ELONGATE MEDICAL DEVICE WITH DISTAL CAP
Technical Field The invention pertains generally to elongate medical devices such as catheters, guidewires, and the like.
Back ound A wide variety of elongate medical devices such as catheters and guidewires have been developed. Such medical devices can be used to facilitate navigation and to treatment within the anatomy of a patient. Because the anatomy of a patient may be very tortuous, it can be desirable to have particular performance features in an elongate medical device. A number of different structures and assemblies for elongate medical devices such as guidewires, catheters, and the like are known, each having certain advantages and disadvantages. There is an ongoing need to provide alternative struct~.res and assemblies.
Summary of Some Embodiments The invention provides several alternative designs, materials and methods of manufacturing alternative medical device structures and assemblies.
Accordingly, an example embodiment of the invention can be found in an elongate medical device that includes an elongate shaft and a distal cap that is formed independently of the elongate shaft. A proximal end of the distal cap includes an aperture that can be configured to fit over a distal end of the elongate shaft. After the distal cap has been formed, it can be secured to the distal end of the elongate shaft.
Another example embodiment of the invention can be found in a guidewire that can be produced by providing a core wire and a distal cap. A proximal end of the distal cap can include an aperture that is configured to fit over a distal end of the core wire. The distal cap can be positioned over the distal end of the core wire by inserting the distal end of the core wire into the aperture, and then the distal cap can be attached 3o to the distal end of the core wire.
Another example embodiment of the invention can be found in a guidewire that has a core wire and an independently formed distal cap. A proximal end of the distal cap can include an aperture that can be configured to accept the end of the core wire, and the distal cap can subsequently be attached to the distal end of the core wire.

Another example embodiment of the invention can be found in a method of producing a guidewire. A core wire can be provided, along with a distal cap. A
proximal end of the distal cap can include an aperture that is configured to fit over a distal end of the core wire. The distal end of the core wire can be inserted into the distal cap aperture, and the distal cap can be attached to the distal end of the core wire.
Another example embodiment of the invention can be found in a method of producing a guidewire. A core wire can be provided, along with a tubular sleeve.
The tubular sleeve can be positioned over a distal end of the core wire, and a metal to ball can be positioned proximate a distal end of the tubular sleeve. At least a portion of the tubular sleeve and the metal ball can be melted via laser welding or plasma welding to form an atraumatic tip.
Another example embodiment of the invention can be found in a guidewire that includes a core wire and a distal cap. A proximal end of the distal cap can i5 include a tubular structure that defines a lumen that is configured to fit over a distal end of the core wire. A distal end of the distal cap can define an arcuate atraumatic surface. The distal cap can be formed independently of the core wire and can be attached to the core wire by inserting the distal end of the core wire into the lumen and attaching the distal cap to the core wire.
20 Another example embodiment of the invention can be found in a guidewire that includes a core wire and means of pro~riding a distal tip to the core wire, the means being formed independently and subsequently secured to a distal end of the core wire.
The above summary of some embodiments is not intended to describe each 25 disclosed embodiment or every implementation of the present invention. The Figures, and Detailed Description which follow more particularly exemplify these embodiments.
Brief Description of the Figuxes The invention may be more completely understood in consideration of 3o the following detailed description of various embodiments of the invention in connection with the accompanying drawings, in which:
Figure 1 is a partially sectioned side view of a distal portion of a guidewire core wire in accordance with one example embodiment of the invention, showing a profile in which a distal portion includes several tapers and a distal-most widened diameter portion;
Figure 2 is a perspective view of a distal cap in accordance with one example embodiment of the invention;
Figure 3 is a cross-sectional view of the distal cap of Figure 2, taken along line 3-3;
Figure 4 is a partially sectioned side view of the guidewire core wire of Figure 1, with the addition of a coil and the distal cap of Figure 2;
Figure 5 is a partially sectioned side view of the guidewire construction of 1o Figure 4, with the addition of a polymer sleeve or sheath;
Figure 6 is a partially sectioned side view of another example guidewire construction having a polymer sheath;
Figure 7 is a partially sectioned side view of another example guidewire construction, showing an alternative tip configuration;
15 Figure 8 is a partially sectioned side view of another example guidewire construction, showing an alternate distal cap design;
Figure ~ is a partially sectioned side view of another example guidewire construction, showing an alternative tip configuration;
Figure 10 is a partially sectioned side view of another example guidewire 20 construction, showing an alternative tip configuration prior to forming the atraumatic portion;
Figure 11 is a partially sectioned side view of the guidewire construction of Figure 10, shown after the forming of the atraumatic portion;
Figure 12 is a partially sectioned side view of another example guidewire 25 construction showing an alternative tip configuration prior to forming the atraumatic portion;
Figure 13 is a partially sectioned side view of the guidewire construction of Figure 12, shown after the forming of the atraumatic portion;
Figure 14 is a cross-sectional exploded view of some of the components of 30 another example medical device;
Figure 15 is a cross-sectional side view depicting the device shown in Figure 14 partially assembled;
Figure 16 is a cross-sectional side view of the example medical device of Figures 14 and 15 including a covering; and Figure 17 is a cross-sectional side view of another example medical device.
Detailed Description of Some Embodiments For the following defined terms, these definitions shall be applied, unless a different definition is given in the claims or elsewhere in this specification.
All numeric values are herein assumed to be modified by the term "about", whether or not explicitly indicated. The term "about" generally refers to a range of numbers that one of skill in the art would consider equivalent to the recited value (i.e., having the same function or result). In many instances, the terms "about" may l0 include numbers that are rounded to the nearest significant figure.
The recitation of nunnerical ranges by endpoints includes all numbers within that range (e.g. 1 to 5 includes 1, 1.5, 2, 2.75, 3, 3.80, 4, and 5).
As used in this specification and the appended claims, the singular forms "a", "an", and "the" include plural referents unless the content clearly dictates otherwise.
As used in this specification and the appended claims, the teen "or" is generally employed in its sense including "and/or" unless the content clearly dictates otherwise.
The following description should be read with reference to the drawings wherein like reference numerals indicate like elements throughout the several views.
The drawings, which are not necessarily to scale, depict illustrative but non-limiting ennbodiments of the claimed invention.
For e~~ample, although discussed with specific reference to guidewires in the particular embodiments described herein, the invention may be applicable to a variety of medical devices that are adapted to be advanced into the anatomy of a patient through an opening or lumen. For example, the invention may be applicable to fixed wire devices, catheters (e.g. balloon, stmt delivery, etc.) drive shafts for rotational devices such as atherectomy catheters and IVLJS catheters, endoscopic devices, laproscopic devices, embolic protection devices, spinal or cranial navigational devices, and other such devices.
Refer now to Figures 1-4, which illustrate components of one example 3o embodiment of a guidewire including a core wire 10, a distal cap 30 connected to the distal end of the core wire 10 and other structure such as a coil. Figure 1 illustrates a distal portion of a guidewire core wire 10 that has a distal end 12 and a proximal end 14.
As shown, the core wire 10 has a proximal constant diameter section 16, an intermediate constant diameter section 20 and a distal constant diameter section 24. A
proximal taper section 18 adjoins the proximal constant diameter section 16 and the intermediate constant diameter section 20. An intermediate taper section 22 adjoins the intermediate constant diameter section 20 and the distal constant diameter section 24. In some embodiments, the constant diameter section 24, or a portion thereof, can be formed into a ribbon to enhance lateral flexibility.
The core wire 10 also has a widened diameter portion 28 that is positioned at the distal end 12 of the core wire 10 and that adjoins a distal taper section 26 that is l0 positioned between the widened diameter portion 28 and the distal constant diameter section 24. The widened diameter portion 28 can act as a heat sink in certain embodiments that use certain attachment techniques using heat to attach the distal cap 30, as discussed below, but this is not necessary.
~ne of skill will recognize that a guidewire core wire can have a profile different from that illustrated in Figure 1. For example, the core wire 10 can be continuously tapered, can have a tapered section or a number or series of tapered sections of differing diameters, or can have a constant diameter. In some embodiments, the core wire 10 can be tapered or otherwise fol-med to have a geometry that decreases in cross sectional area toward the distal end thereof.
If tapered, the core wire 10 can include a uniform or a non-uniform transition between the S~~tl~115, depending on the transition characteristics desired. For example, the core wire 10 can be linearly tapered, tapered 111 a curvlhnear fashion, or tapered in a step-wise fashion. The angle of any such tapers can vary, depending upon the desired flexibility charactel-istics. The length of the taper may be selected to obtain a more (longer length) or less (shorter length) gradual transition in stiffness.
The stl-ucture used to construct the core wire 10 can be designed such that a proximal portion 13 is relatively stiff for pushability and torqueability, and a distal portion 11 is relatively flexible by comparison for better lateral trackability and steerability. For example, in some embodiments, the proximal portion 13 has a 3o constant or generally uniform diameter along its length to enhance stiffness.
However, embodiments in which the proximal portion 13 has a tapered portion or a series of tapered portions are also contemplated. The diameter of the proximal portion 13 can be sized appropriately for the desired stiffness characteristics dependent upon the material used. For example, in some embodiments, the proximal portion 13 can have a diameter in the range of about 0.010 to about 0.025 inches or greater, and in some embodiments, in the range of about 0.010 to about 0.018 inches or greater.
The distal portion 11 can likewise be constant diameter, can be continuously tapered, or can have a tapered section or a number or a series of tapered sections of differing diameters. In embodiments where the structure of core wire 10 is designed such that the distal portion 11 is relatively flexible by comparison to the proximal portion 13, the distal portion 11 can include at least one tapered or reduced diameter portion for better flexibility characteristics.
l0 The tapered and constant diameter portions can be formed by any one of a number of different techniques, for example, by centerless grinding, stamping and the like. A centerless grinding technique can utilize an indexing system employing sensors (e.g., optical/reflective, magnetic) to avoid excessive grinding. In addition, the centerless grinding technique can utilize a CBN or diamond abrasive grinding wheel that is well shaped and dressed to avoid grabbing the core wire 10 during the grinding process. Moreover, some stamping techniques can be used to form a portion of the guidewire, for example, a distal portion, into a ribbon or other like structure.
The lengths of the proximal and distal portions 13, 11 are typically dictated by the length and flexibility characteristics desired in the final medical device. In some 2o embodiments, the proximal portion 13 can have a length in the range of about SO to about 300 centimeters, and the distal portion 11 can hive a length in the range of about 3 to about 50 centimeters.
The core wire 10 can have a solid cross-section as shown,' but in some embodiments, can have a hollow cross-section. In yet other embodiments, core wire .
10 can include a combination of areas having solid cross-sections and hollow cross sections.
In some embodiments, the core wire 10 can be formed of any suitable metallic, polymeric or composite material. In some embodiments, part or all of the core wire 10 can be formed of a metal or a metal alloy. Some examples of suitable 3o metals and metal alloys include stainless steel, such as 304V, 304L, and stainless steel; alloys including nickel-titanium alloy such as linear elastic or superelastic (i.e. pseudoelastic) nitinol; nickel-chromium alloy; nickel-chromium-iron alloy; cobalt alloy; tungsten or tungsten alloys; MP35-N (having a composition of about 35% Ni, 35% Co, 20% Cr, 9.75% Mo, a maximum 1% Fe, a maximum 1% Ti, a maximum 0.25% C, a maximum 0.15% Mn, and a maximum 0.15% Si); hastelloy;
monel 400; inconel 625; or the like; or other suitable material. The particular material used can be chosen in part based on the desired flexibility requirements of the core wire 10. In some particular embodiments, the core wire 10 can be formed from a superelastic or linear elastic nickel-titanium alloy, for example, linear elastic or superelastic (i.e. pseudoelastic) nitinol.
The word nitinol was coined by a group of researchers at the United States Naval Ordinance Laboratory (NOL) who were the first to observe the shape memory behavior of this material. The word nitinol is an acronym including the chemical l0 symbol for nickel (Ni), the chemical symbol for titanium (Ti), and an acronym identifying the Naval Ordinance Laboratory (NOL).
Within the family of commercially available nitinol alloys, is a category designated "linear elastic" which, although is similar in chemistry to conventional shape memory and superelastic varieties, exhibits distinct and useful mechanical properties. ~y skilled applications of cold work, directional stress, and heat treatment, the wire is fabricated in such a way that it does not display a substantial "SUperelaStlC plateau" or "flag region" in its stress/strain curve. Instead, aS
recoverable strain increases, the stress continues to increase in an essentially linear relationship until plastic deformation begins. In some embodiments, the linear elastic nickel-titanium alloy is an alloy that does not show any martensite/austenite phase changes that are detectable by I~SC and I~I~IIT~ analysis over a large temperature r ange.
For example, in some embodiments, there is no martensite/austenite phase changes detectable by I~SC and 17MTA analysis in the range of about -60°C to about ~5 120°C. The mechanical bending properties of such material are therefore generally inert to the effect of temperature over this very broad range of temperature.
In some particular embodiments, the mechanical properties of the alloy at ambient or room temperature are substantially the same as the mechanical properties at body temperature. In some embodiments, the use of the linear elastic nickel-titanium alloy 3o allows the guidewire to exhibit superior "pushability" around tortuous anatomy.
In some embodiments, the linear elastic nickel-titanium alloy is in the range of about 50 to about 60 weight percent nickel, with the remainder being essentially titanium. In some particular embodiments, the composition is in the range of about 54 to about 57 weight percent nickel. One example of a suitable nickel-titanium alloy is FHP-NT alloy cormnercially available from Furukawa Techno Material Co. of I~anagawa, Japan. Some examples of nickel-titanium alloys include those disclosed in U.S. Patent Nos. 5,238,004 and 6,508,803, which are incorporated herein by reference. In some other embodiments, a superelastic alloy, for example a superelastic nitinol can be used to achieve desired properties.
In at least some embodiments, portions or all of the core wire 10, or other structures included within the medical device may also be doped with, made of, or otherwise include a radiopaque material. Radiopaque materials are understood to be materials capable of producing a relatively bright image on a fluoroscopy screen or l0 another imaging technique during a medical procedure. This relatively bright image aids the user of device in determining its location. Some examples of radiopaque materials can include, but are not limited to, gold, platinum, palladium, tantalum, tungsten alloy, polymer material loaded with a radiopaque filler, and the like.
In some embodiments, a degree of MRI compatibility can be imparted. For example, to enhance compatibility with Magnetic Resonance Imaging (MRI) machines, it may be desirable to make the core wire 10, or other portions thereof, in a manner that would impart a degree of MRI compatibility. For example, the core wire 10, or portions thereof, may be made of a material that does not substantially distort the image and create substantial artifacts (artifacts are gaps in the image).
Certain ferromagnetic mateuials, for example, may not be suitable because they may create artifacts in an h~flRI image. Core wire 109 or portions thereof9 may also be made from a material that the MRI machine can image. Some materials that exhibit these characteristics include, for example, tungsten, Elgiloy, MP35N, nitinol, and the like, and others.
The entire core wire 10 can be made of the same material, or in some embodiments, can include portions or sections that are made of different materials. In some embodiments, the material used to construct different portions of the core wire 10 can be chosen to impart varying flexibility and stiffness characteristics to different portions of the wire. For example, the proximal portion 13 and the distal portion 11 can be formed of different materials (i.e., materials having different moduli of elasticity) resulting in a difference in flexibility. In some embodiments, the material used to construct the proximal portion 13 can be relatively stiff for pushability and torqueability, and the material used to construct the distal portion 11 can be relatively flexible by comparison for better lateral trackability and steerability. For example, the proximal portion 13 can be formed of, for example, straightened 304v stainless steel wire, and the distal portion 11 can be formed of, for example, a straightened super elastic or linear elastic alloy (e.g., nickel-titanium) wire.
In embodiments where different portions of core wire 10 are made of different material, the different portions can be connected using any suitable connecting techniques. For example, the different portions of the core wire can be connected using welding, soldering, brazing, adhesive, or the like, or combinations thereof.
Additionally, some embodiments can include one or more mechanical connectors or connector assemblies to connect the different portions of the core wire that are made l0 of different materials. The connector can include any structure generally suitable for connecting portions of a guidewire. One example of a suitable structure includes a structure such as a hypotube or a coiled wire which has an inside diameter sized appropriately to receive and connect the different portions of the core wire.
Some methods and structures that can be used to interconnect different shaft sections are disclosed in U.S. Patent Application IVos. 09/972,276, and 10/06,992, which are incorporated herein by reference. Additionally, some methods and structures using expandable alloys to connect guidewire members are disclosed in a IJ.s. Patent Application entitled "C~hIP~SITE l~IIEI~ICAL I~ES~IGE" (Attorney docket number 1001.1546101 ) filed on even date herewith. Additionally, some methods and 2o structures including alternatives structures for connecting medical device sections are disclosed in a LT.S. Patent Application entitled '°AI~TICLTLATII~TG
II~TTP.AC~IZP~I~AL, I~EI~ICAI, I~E~ICE" (Attorney docket no. 1001.166101) filed on even date herewith, which is incorporated herein by reference.
It is to be understood that a broad variety of materials, dimensions and structures can be used to construct suitable embodiments, depending on the desired characteristics. The following examples of some dimensions are included by way of example only, and are not intended to be limiting.
In some embodiments, the core wire 10 can have the general profile set forth in Figure 1. In some example embodiments, the proximal constant diameter section 16 can have a length that is in the range of about 10 to 120 inches and a diameter that is in the range of about 0.010 to about 0.040 inches. The intermediate constant diameter section 20 can have a length that is in the range of about 2 to about 12 inches and a diameter that is in the range of about 0.007 to about 0.025 inches. The distal constant diameter section 24 can have a length that is in the range of about 1 to about 4 inches and a diameter that is in the range of about 0.002 to about 0.004 inches. The heat sink portion 28 can have a length that is in the range of about 0.025 to about 0.25 inches and a diameter that is in the range of about 0.005 to about 0.20 inches. The proximal taper section 18, the intermediate taper section 22 and the distal taper section 26 can each have a length that is in the range of about 0.5 to about 4 inches.
Figures 2 and 3 illustrate an embodiment of a distal cap 30 that is adapted and configured to fit over the distal end 12 of the core wire 10. Figure 2 is a perspective view of the distal cap 30 while Figure 3 is a cross-sectional view. The distal cap 30 has a proximal end 32 and a distal end 34. The distal end 34 can be configured to provide an atraumatic tip once the distal cap 30 has been secured to the core wire 10 (as discussed hereinafter). In some embodiments, as illustrated, the distal end 34 of the distal cap 30 can have a hemispherical configuration.
The proximal end 32 of the distal cap 30 can be adapted and configured to interact with the distal end 12 of the core wire 10. In some embodiments, the proximal end 32 of the distal cap 30 is configured such that the distal end 12 of the core wire 10 can fit at least partially inside the distal cap 30. In some embodiments, the proximal end 32 of the distal cap 30 can include a lumen or aperture 36 that extends at least partially into the distal cap 30 and that is surrounded by a shell 38.
The shell 38 can in some embodiments have an annular or tubular form.
2o In some illustrative but non-limiting embodiments, the distal cap 30 can have a proximal portion that is substantially cylindrical in shape, with an outer diameter in the range of about 0.010 to about 0.040 inches and a length that is in the range of about 0.025 to about 0.250 inches. The aperture 36 can have an inner diameter that is in the range of about 0.002 to about 0.150 inches and a depth that is in the range of about 0.010 to about 0.150 inches.
The distal cap 30 can be formed from a variety of different materials, depending on desired performance characteristics. suitable materials can include polymers, metals and metal alloys, such as those discussed with respect to the core wire 10, as well as other materials such as composites, amorphous or polycrystalline inorganics, and carbons such as pyrolitic carbon. Some illustrative but non-limiting examples of suitable metals and metal alloys include stainless steel, nickel-titanium alloys, niclcel-chromium alloys, nickel-chromium-iron alloy, cobalt alloy, tungsten or tungsten alloys, Inconel 625, and other suitable materials.

In at least some embodiments, portions or all of the distal cap 30 can be doped with, made of, or otherwise include a radiopaque material, as discussed with respect to the core wire 10. Some examples of radiopaque materials can include, but are not limited to, gold, platinum, palladium, tantalum, tungsten alloy, polymer material loaded with a radiopaque filler, and the like.
In some embodiments, a degree of MRI compatibility can be imparted. For example, to enhance compatibility with Magnetic Resonance Imaging (MRI) machines, it can be desirable to make the distal cap 30 in a manner that would impart a degree of MRI compatibility, as discussed with respect to the core wire 10.
Some to suitable materials include, for example, tungsten, Elgiloy, MP35N, nitinol, and the like, and others.
In some embodiments, the distal cap 30 can be formed of a material such as a metallic material that is amenable, for a particular attachment method, to being welded to the distal end 12 of the core wire 10, as will be discussed in greater detail hereinafter. In some particular embodiments, it can be beneficial but not necessary for the distal cap 30 to be formed of the same metal or metal alloy as the distal end 12 of the core wire 10.
For example, if the core wire 10 is forned of stainless steel, it call be beneficial for the distal cap 30 to be formed of stainless steel or a material compatible therewith. In other embodiments, both of the distal cap 30 and the distal end 12 of the core wire 10 can be formed of the same metal alloy, such as nitinol.
A variety of different processes, such as deep drawing, roll forming or metal stamping can be used to form the distal cap 30. In some embodiments, the distal cap can be metal injection molded. It is contemplated that the distal cap 30 can be 25 formed via a casting process, with the aperture 36 formed through a drilling process.
In some embodiments, the distal cap 30 can be formed using processes such as impact extrusion, cold forming or electrodeposition.
Figure 4 illustrates one example embodiment of a guidewire 52 including the distal cap 30 in position over the distal end 12 of the core wire 10. In some 3o embodiments, the distal cap 30 can be positioned such that its proximal end overlaps a portion of the heat sink 28. As illustrated, the distal cap 30 extends proximally such that the proximal end 32 of the distal cap 30 is positioned at a midpoint 40 that is approximately midway between the distal end 42 of the heat sink 28 and the proximal end 44 thereof. In other embodiments, the proximal end 32 can extend further proximally on the core wire 10, or may end at a more distal portion on the core wire 10.
A coil 46 having a distal end 48 and a proximal end 50 is positioned such that the distal end 48 of the coil 46 overlaps a portion of the heat sink 28. In some embodiments, the distal end 48 of the coil 46 can be positioned proximate the midpoint 40 and thus can be positioned proximate the proximal end 32 of the distal cap 30. The proximal end 50 of the coil 46 can in some embodiments be positioned proximate the proximal taper section 18. One of skill will recognize that the coil 46 can be positioned such that its proximal end 50 is proximate the intermediate taper l0 section 22, or that a guidewire can include both a coil 46 as illustrated and one or more additional coils, for example, disposed about or under the coil 46.
The coil 46 can be formed of a variety of materials including metals, metal alloys, polymers, and the like. Some examples of material for use in the coil include stainless steel, such as 304V, 304L and 316L stainless steel, nickel-chromium alloy, nickel-chromimn-iron alloy, cobalt alloy, tungsten or tungsten alloys, MP35-N, Ilastelloy, Monel 400, Inconel 625, or other suitable materials.
Some additional examples of suitable material include straightened super elastic, i.e. pseudoelastic, or linear elastic alloy (e.g., nickel-titanium) wire, or alternatively, a polymer material, such as a high performance polymer. In some embodiments, the coil 46 or portions thereof can be made of or include or be coated with a radiopaque material such as gold, platinmn, tungsten, or the like, or alloys thereof. In some embodiments, the coil 4~6 can be made of a material that is compatible with the core wire 10 and the distal cap 30.
In some embodiments, it can be advantageous for the coil 46 to include radiopaque materials, as discussed with respect to the core wire 10. Some examples of radiopaque materials can include, but are not limited to, gold, platinum, palladium, tantalum, tungsten alloy, polymer material loaded with a radiopaque filler, and the like.
In some embodiments, a degree of MRI compatibility can be imparted. For example, to enhance compatibility with Magnetic Resonance Imaging (MRI) machines, it can be desirable to make the coil 46 in a manner that would impart a degree of MRI compatibility, as discussed with respect to the core wire 10.
Some suitable materials include, for example, tungsten, Elgiloy, MP35N, nitinol, and the like, and others.

The coil 46 can be formed of round or flat ribbon ranging in dimensions to achieve desired characteristics, such as flexibility. A round ribbon can be considered as having a round or oval cross-sectional shape while a flat ribbon can be considered as having a rectangular cross-sectional shape. In some embodiments, the coil 46 can be a round ribbon in the range of about 0.0005-0.004 inches in diameter, and can have a length in the range of about 0.1 to about 20 inches, however, other dimensions are contemplated.
The coil 46 can be wrapped in a helical fashion by conventional winding techniques. The pitch of adjacent turns of the coil 46 may be tightly wrapped so that to each turn touches the succeeding turn or the pitch may be set such that the coil 46 is wrapped in an open fashion.
To form the guidewire assembly 52 shown in Figure 4, the distal cap 30 and the coil 46 can be positioned proximate the core wire 10 as illustrated. The distal cap 30 and the coil 46 can be secured to the core wire 10 in any suitable manner, including for example welding, soldering, brazing, crimping, friction fitting, adhesive bonding, mechanical interlocking and the like. In these and some other example embodiments, securing the distal cap 30 to the core wire 10 may include the use of a connector and/or an expandable alloy, for example a bismuth alloy. Some examples of methods, techniques, and structures that can be used to interconnect different portions of a guidewire are disclosed in a U.S. Patent Application entitled "Composite Medical I~evice'9 (Attorney docket number 1001.1546101) filed on even date with this application and which is hereby incorporated by reference, and in U.S. Patent Application lVos. 09/972,276 and 10/086,992, which are incorporated herein by reference.
In some embodiments, the coil 46 and the cap 30 are welded to the core wire 10. It is to be appreciated that various welding processes can be utilized. In general, welding refers to a process in which two materials such as metal or metal alloys are joined together by heating the two materials sufficiently to at least partially melt adjoining surfaces of each material. A variety of heat sources can be used to melt the 3o adjoining materials. Examples of welding processes that can be suitable in some embodiments include LASER welding, resistance welding, TIG welding, microplasma welding, electron beam, and friction or inertia welding.
LASER welding equipment that may be suitable in some embodiments is commercially available from Unitek Miyachi of Monrovia, California and Rofin-Sinar Incorporated of Plymouth, Michigan. Resistance welding equipment that may be useful in some embodiments is commercially available from Palomar Products Incorporated of Carlsbad, California and Polaris Electronics of Olathe, Kansas. TIG
welding equipment that may be useful in some embodiments is cormnercially available from Weldlogic Incorporated of Newbury Park, California. Microplasma welding equipment that may be useful in some embodiments is cormnercially available from Process Welding Systems Incorporated of Smyrna, Tennessee.
In some embodiments, laser or plasma welding can be used to secure the distal cap 30, the coil 46 and the core wire 10 securely together. In laser welding, a 1o light beam is used to supply the necessary heat. Laser welding can be beneficial in the processes contemplated by the invention, as the use of a laser light heat source can provide pinpoint accuracy. In some embodiments, laser diode soldering' can be useful, again for pinpoint accuracy. Further, securing the distal cap 30, coil 46, and the core wire 10 together may include the use of expandable alloys (e.g., bismuth alloys) similar to what is described above.
Figure 5 shows an alternative guidewire assembly with an optional polymer sleeve 54 while Figure 6 shows an alternative guidewire assembly having a polymer sheath 53. In this embodiment, no coil is included. Instead, a polymer tip guidewire is formed by including the polymer sheath 53 that forms a rounded tip over the distal cap 30. The polymer sheath 53 or polyner sleeve 54 can be made from any material that can pro-~ide the desired strength, flexibility or other desired characteristics. The sheath 53 or polyner sleeve 54~ can in some non-limiting embodiments have a length that is in the range of about 3 to about 15 inches and can have an inner diameter that is in the range of about 0.002 to about 0.025 inches and an outer diameter that is in the range of about 0.010 to about 0.040 inches.
The use of a polymer can serve several functions, such as improving the flexibility properties of the guidewire assembly. Choice of polymers for the sleeve 53 or sheath 54 will vary the flexibility. For example, polymers with a low durometer or hardness will make a very flexible or floppy tip. Conversely, polymers with a high 3o durometer will make a tip which is stiffer. The use of polymers for the sleeve can also provide a more atraumatic tip for the guidewire. An atraumatic tip is better suited for passing through fragile body passages. Finally, a polymer can act as a binder for radiopaque materials, as discussed in more detail below.

Some suitable materials include polymers, and like material. Examples of suitable polymer material include any of a broad variety of polymers generally known for use as guidewire polymer sleeves. In some embodiments, the polymer material used is a thermoplastic polymer material. Some examples of some suitable materials include polyurethane, elastomeric polyamides, bloclc polyamidelethers (such as Pebax), silicones, and co-polymers. The sleeve may be a single polymer, multiple layers, or a blend of polymers. By employing careful selection of materials and processing techniques, thermoplastic, solvent soluble, and thermosetting variants of these materials can be employed to achieve the desired results.
l0 Further examples of suitable polymeric materials include but are not limited to poly(L-lactide) (PLLA), poly(D,L-lactide) (PLA), polyglycolide (PGA), poly(L-lactide-co-D,L-lactide) (PLLA/PLA), poly(L-lactide-co-glycolide) (PLLAIPGA), poly(D, L-lactide-co-glycolide) (PLA/PGA), poly(glycolide-co-trimethylene carbonate) (PGA/PTMC), polyethylene oxide (PEO), polydioxanone (PDS), is polycaprolactone (PCL), polyhydroxylbutyrate (PHBT), poly(phospha~ene), poly D,L-lactide-co-caprolactone) (PLA/PCL), poly(glycolide-co-caprolactone) (PGA/PCL), polyanhydrides (PAIV), poly(ortho esters), polyphosphate ester), poly(amino acid), poly(hydroxy butyrate), polyacrylate, polyacrylamid, poly(hydroxyethyl methacrylate), polyurethane, polysiloxane and their copolymers.
In some embodiments, the sheath 53, sleeve 54, or portions thereof, can include, or be doped with, radiopaque imaterial to make the sheath 53, sleeve 54, or portions thereof, more visible when using certain imaging techniques, for example, fluoroscopy techniques. Any suitable radiopaque material known in the art can be used. Some examples include precious metals, tungsten, barium subcarbonate powder, and the like, and mixtures thereof. In some embodiments, the polymer can include different sections having different amounts of loading with radiopaque material. For example, the sheath 53 or sleeve 54 can include a distal section having a higher level of radiopaque material loading, and a proximal section having a correspondingly lower level of loading.
In some embodiments, it is also contemplated that a separate radiopaque member or a series of radiopaque members, such as radiopaque coils, bands, tubes, or other such structures could be attached to the guidewire core wire 10, or incorporated into the core wire by plating, drawing, forging, or ion implantation techniques.

The sheath 53 or sleeve 54 can be disposed around and attached to the guidewire assembly 52 using any suitable technique for the particular material used.
In some embodiments, the sheath 53 or- sleeve 54 can be attached by heating a sleeve of polymer material to a temperature until it is reformed around the guidewire assembly 52. In some embodiments, the sheath 53 or the sleeve 54 can be secured to the core wire 10 using a suitable adhesive. In some other embodiments, the sheath 53 or sleeve 54 can be attached using heat shrinking techniques. In other embodiments, the sheath 53 or sleeve 54 can be co-extruded with the core wire 10. The sleeve 54 can be finished, for example, by a centerless grinding or other method, to provide the l0 desired diameter and to provide a smooth outer surface.
A guidewire in accordance with some embodiments of the invention can optionally include a coating layer such as a lubricious coating layer over part or all of the guidewire assembly 52 or even over part or all of the polymer sheath 53 or sleeve 54. Hydrophobic coatings such as fluoropolymers provide a dry lubricity which improves guide wire handling and device exchanges. Lubricious coatings improve steerability and improve lesion crossing capability. Suitable lubricious polymers are well known in the art and may include hydrophilic polymers such as polyarylene oxides, polyvinylpyrohidones, polyvinylalcohols, hydroxy alkyl cellulosics, algins, saccharides, caprolactones, and the like, and mixtures and combinations thereof.
Hydrophilic polymers may be blended among themselves or with formulated amounts of water insoluble compounds (inchiding some polyners) to yield coatings with siitable lubricity, bonding, and solubility. In some embodiments, the more distal portion of the guidewire is coated with a hydrophilic polymer as discussed above, and the more proximal portions is coated with a fluoropolymer, such as ?5 polytetrafluroethylene (PTFE).
Figures 7 through 13 illustrate other example embodiments of the invention.
Figures 7-9, for example, shows alternate embodiments in which a core wire 56 has, in sequence, a proximal constant diameter section 58, an adjoining proximal taper section 60, an intermediate constant diameter section 62, an adjoining distal taper 3o section 64 and a distal constant diameter section 66. Unlike the core wire 10 of the previous Figures, the core wire 56 has no enlarged portion or heat sink at the distal end thereof. The core wire 56 can be manufactured from any suitable material, such as the metals and metal alloys discussed with respect to the core wire 10.
Figures 7, 8 and 8 each illustrate particular embodiments of providing and securing a distal cap to the core wire 56.
In Figure 7, a coil 70 is positioned over the distal constant diameter section 66.
The coil 70 has a distal end 72 that can be positioned proximate a distal end 68 of the distal constant diameter section 66 and a proximal end 74 that can be positioned proximate the distal taper section 74. One of skill will recognize that the proximal end 74 of the coil 70 could extend further in a proximal direction, depending on the exact profile of the core wire 56. The coil 70 can be manufactured using the materials and parameters previously discussed with respect to the coil 46.
1o In this illustrative embodiment, a distal cap 76 having a distal end 78 and a proximal end 80 is adapted and configured to fit over the distal end 68 of the distal constant diameter section 66. In particular, the proximal end 80 of the distal cap 76 includes an aperture 82 that is sized and configured to accept the distal end 68 of the distal constant diameter section 66 as well as the distal end 72 of the coil 70. The distal cap 76 can be manufactured using similar materials and procedures as previously discussed with respect to the distal cap 30.
The distal cap 76 and the coil 70 can be secured to the core wire 56 in any suitable manner, including those described above, for example welding, soldering, brazing, crimping, friction fitting, adhesive bonding and the like. In some 2o embodiments, laser or plasma welding can be used to secure the distal cap 76, the coil 70 and the core wire 56 securely together. l-additionally, securing the distal cap 76, the coil 70, and the core wire 56 may include the use of expandable alloys (e.g., bismuth alloys) similar to what is described above.
In the embodiment shown in Figure 7, the guidewire includes a polymeric layer 55. It is to be understood that the guidewire can include one or more additional polymeric layers as discussed previously. Ii~Ioreover, such a guidewire can be partially or completely coated with a lubricious or hydrophilic coating as described hereinabove.
In Figure 8, a distal sleeve 84 having a distal end 86 and a proximal end 88 is 3o positioned over the distal constant diameter section 66 of the core wire 56. The distal sleeve 84 can be positioned such that the distal end 86 of the distal sleeve 84 is proximate the distal end 68 of the core wire 56. The distal sleeve 84 can be formed of any suitable material, such as the metals and metal alloys previously discussed.

As illustrated, the distal sleeve 84 can have an outer diameter that approximates an outer diameter of the intermediate constant diameter section 62. As a result, a coil 90 having a distal end 92 and a proximal end 94 can be positioned such that the distal end 92 of the coil 90 is proximate a midpoint of the distal sleeve 84 and the proximal end 94 of the coil 90 is proximate the distal taper section 60.
The coil 90 can be manufactured as discussed for example with respect to the coil 46.
A distal cap 96 has a distal end 98 and a proximal end 100. In some embodiments, the distal end 98 of the distal cap 96 can form an atraumatic tip and can in particular embodiments form a hemispherical shape. In some embodiments, the l0 proximal end 100 of the distal cap 96 can be configured to fit securely over the distal end 68 of the core wire 56 and the distal end 86 of the distal sleeve 84. In particular, the proximal end 100 of the distal cap 96 can include an aperture 102 that is sized to fit securely over the distal end 86 of the distal sleeve 84. The distal cap 96 can be manufactured as previously discussed with respect to the distal cap 30.
1s In the embodiment shown in Figure 8, it is to be understood that such a guidewire can include one ox more polymeric layers as discussed previously and may or may not include a coil 90 as shown. hlloreover, such a guidewire can be partially or completely coated with a lubricious or hydrophilic coating as described hereinabove.
2o Figure 9 shows a core wire 56 and coil 90 as described in relation to the previous Figures. A distal cap 104 has a distal end 106 and a proximal end 108. In some embodiments, the distal end 106 of the distal cap 104 can form an atraumatic tip and can in particular embodiments form a hemispherical shape. The proximal end 108 of the distal cap 104 can be configured to fit over the distal end 68 of the core 2s wire 56. The distal cap 104 can be manufactured as previously discussed with respect to the distal cap 30.
In some embodiments, the proximal end 108 of the distal cap 104 can include an aperture 110 that is configured to accept the distal end 68 of the core wire 56. In particular, the aperture 110 can have an inner diameter that approximates an outer 3o diameter of the core wire 56 and a depth that is sufficient to permit the distal end 68 of the core wire 56 to penetrate the distal cap 104. The proximal end 108 of the distal cap 104 can also include a shoulder 112 that can be configured to accept the distal end 92 of the coil 90.

Once the distal cap 104 has been positioned over the core wire 56 and under the coil 90, the distal cap 104 and the coil 90 can be secured to the core wire 56 in any suitable manner, including for example welding, soldering, brazing, crimping, friction fitting, adhesive bonding and the like or other technique, for example those described above in relation to method of the distal cap. In some embodiments, laser or plasma welding can be used to secure the distal cap 104, the coil 90 and the core wire 56 securely together.
In the embodiment shown in Figure 9, it is to be understood that such a guidewire can include one or more polymeric layers as discussed previously.
l0 Additionally, in some embodiments, a coil is not used, and a polymer sheath is secured to the distal tip. Moreover, such a guidewire can be partially or completely coated with a lubricious or hydrophilic coating as described hereinabove.
Figures 10-13 illustrate further embodiments of the invention in which a distal tip is partially formed, is attached to a core wire and is further processed to achieve its final desired shape.
Figures 10-11 illustrate a core wire 112 that includes a proximal constaazt diameter section 114, a proxunal taper section 116, an intermediate constant diameter section 118, an intermediate taper section 120, a distal constant diameter section 122, a distal taper section 124 and a heat sink portion 126 having a distal end 127. The 2o core wire 112 can be manufactured from any suitable metal or metal alloy, as discussed previously.
In Figure 10, a distal sleeve 128 having a distal end 130 and a proximal end 132 is positioned proximate the distal end 127 of the heat sink portion 126 and in some embodiments the distal end 130 of the distal sleeve 128 can extend distally beyond the distal end 127 of the heat sink portion 126. The distal sleeve 128 can be attached or connected to the core wire 112 using any suitable technique, for example, those described above. The distal sleeve 128 can be manufactured from any suitable metal or metal alloy, as discussed previously.
A metal ball 134 (see Figure 10) can be positioned proximate the distal end 130 of the distal sleeve 128. In some embodiments the metal ball 134 can be in contact with the distal end 127 of the heat sink portion 126 while in other embodiments the metal ball 134 is held away from the heat sink portion 126 by the distal sleeve 128. The metal ball 134 can be formed of any suitable material, including metals and metal alloys. In some embodiments, it can be beneficial but not necessary for the metal ball 134 to be formed of the same material as the distal sleeve 128.
In some embodiments, the metal ball 134 can be formed from a non-fusible shape such as a sphere or ovoid that has been coated with a fusible alloy such as solder. Such a metal ball 134 can be secured by re-flowing the solder. In some embodiments, the solder could be a bismuth composition as described previously. It is contemplated that the metal ball 134 itself could be formed from a bismuth fusible alloy.
A coil 136 having a distal end 138 and a proximal end 140 can be positioned over the core wire 112 such that the distal end 138 of the coil 136 is positioned proximate the distal end 130 of the distal sleeve 128 and that the proximal end 140 of the coil 136 is positioned proximate the proximal taper section 116. The coil 136 can be manufactured in accordance with the materials and parameters discussed previously.
Figure 11 shows an atraumatic distal cap 142 that has been formed as a result of at least partially melting the metal ball 134 and the distal sleeve 128.
The metal ball 134 and the distal sleeve 128 can be at least partially melted using a variety of techniques. In some embodiments, the metal ball 134 and the distal sleeve 128 can be partially melted using a welding process, such as laser welding or plasma welding. In 2o some embodiments (not illustrated), it is contemplated that the distal end 138 of the coil 136 and even the distal end 127 of the heat sink portion 126 may also partially melt to form a portion of the atraumatic distal cap 142.
In the embodiment shown in Figures 10-11, it is to be understood that such a guidewire can include one or more polymeric layers as discussed previously and does not necessarily include a coil, especially if the guidewire has a polymer tip.
Moreover, such a guidewire can be partially or completely coated with a lubricious or hydrophilic coating as described hereinabove.
Figures 12 and 13 illustrate a core wire 144 that includes a proximal constant diameter section 146, a proximal taper section 148, an intermediate constant diameter 3o section 150, a distal taper section 152 and a distal constant diameter section 154 having a distal end 156. The core wire 144 can be manufactured from any suitable metal or metal alloy, as discussed previously.
In Figure 12, a preformed distal cap blank 164 has been positioned over the distal end 156 of the distal constant diameter section 154. The distal cap blank 164 can be formed of any suitable material, including the metals and metal alloys discussed with respect to other embodiments of the invention. In some embodiments, the distal cap blank 164 can include an aperture 166 that has been formed in a proximal end 165 of the distal cap blank 164. As illustrated, the distal cap blank 164 has a distal end 163 having a squared-off profile. In other embodiments, the distal cap blank 164 can be formed having a hemispherical or otherwise curved distal end 163.
A coil 158 having a distal end 160 and a proximal end 162 can be positioned over the core wire 144 such that the distal end 160 of the coil 158 is positioned to proximate the distal end 163 of the distal cap blank 164 and that the proximal end 162 of the coil 158 is positioned proximate the proximal taper section 148. The coil 158 can be manufactured in accordance with the materials and parameters discussed previously.
Figure 13 shows an atraumatic distal cap 168 that has been formed as a result of at least partially melting the distal cap blank 164. In some embodiments (not illustrated), it is contemplated that the distal end 160 of the coil 158 may also partially melt to form a portion of the atraumatic distal cap 168.
In the embodiments shown, it is to be understood that such a guidewire can include one or more polymeric layers as discussed previously. Moreover, such a 2o guidewire can be partially or completely coated with a lubricious or hydrophilic coating as described hereinabove.
Figure 14 is an exploded view of some of the components of another example medical device 170, which is similar to the other devices described herein.
Device 170 may include a core wire 172 and a distal cap 174. Core wire 172 can be manufactured from any suitable materials including those described herein. For example, core wire 172 may include a metal (such as stainless steel, nickel-titanium alloy, etc.), polymer, metal-polymer composite, and the like. In at least some embodiments, core wire 172 may include a proximal section 176, a distal section 178, and an enlarged distal end section 180. Additionally, distal section 178 may include a ribbon 177 formed in the wire 172 or otherwise disposed between enlarged distal section 180 and distal section 178. Proximal section 176 may be similar to other proximal core wire sections described herein. For example, proximal section 176 may be configured to be sufficiently stiff to provide device 170 with the desired level of pushability and torquability. Similarly, tapered distal section 178 may be tapered, for example, in order to increase the distal flexibility of device. Enlarged distal end section 180 may be configured to attach to distal cap 174 as described in more detail below. In some embodiments, a ribbon can be formed or otherwise disposed adjacent cap 174 and core wire 172. For example, the ribbon may be disposed behind cap 174.
Distal cap 174 may include a tubular body portion 182 and a generally atraumatic tip portion 184. In some embodiments, body portion 182 may comprise a hypodermic tube made of a suitable material. Some examples of suitable materials include stainless steel, nickel-titanium alloy, nickel-chromium alloys such inconel (including inconel 625), or any other suitable material including any of those to described herein. Tip portion 184 may include a solder ball or other suitable structure that can be coupled to body portion 182. Tip portion 184 can be coupled to body portion 182 in any suitable manner. For example, tip portion 184 can be soldered, welded (including plasma, laser, and other known welding techniques), thermal bonding, chemical bonding, adhesive bonding, mechanical bonding, frictional fitting, and the like. Distal cap 174 can be formed prior to attaclmnent to core wire 172.
Distal cap 174 may be coupled to core wire 172 as shown in Figure 15. In at least some embodiments, body portion 182 of distal cap 174 can be disposed over enlarged distal end section 180. According this embodiment, enlarged distal end section 180 may be sized to fit within tubular body portion 182. Cap 174 can be coupled, attached, or otherwise secured to core wire 172 in essentially any known v~ay including those listed above. For example, distal end section 180 and body portion 182 can be coupled by laser welding. In this and other embodiments that include the use of thermal energy or otherwise including heat, enlarged distal end section 180 may act as a heat sink to help absorb and distribute the heat generated by the coupling process. This may help reduce the possibility that heat could damage core wire 172.
A covering or sheath 186 may' be disposed over a portion of core wire 172 and/or cap 174 as shown in Figure 16. Similar to what is described above, sheath 186 may be made of essentially any appropriate material including suitable polymers and 3o the like. In some embodiments, sheath 186 may be disposed over tapered distal section 178 and extend distally to define a generally rounded tip for device 170.
Additionally, sheath 178 may extend proximally toward proximal section 176.
Another example medical device 270 is illustrated in Figure 17. Device 270 is similar to device 170, except that covering 286 may comprise a spring tip that includes a coil 286. Coil 286 may be made from suitable materials including those listed herein and may extend, for example, distally from an attachment point adjacent proximal section 176 over distal section 178. The configuration of coil 286 may vary.
For example, coil 286 may have essentially any appropriate shape, thickness, length, pitch, material composition, and the like including any of the various properties and configurations described herein.
Distal cap 274 may include tip portion 284. In some embodiments, tip portion 284 may be larger than tip portion 184 (as shown in Figures 14-16) so that it has a width or outside diameter that is greater than body portion 282. According to this to embodiment, tip portion 284 may extend laterally beyond body portion 282 and define a shoulder region 290. Attaching cap 274 to core wire 172, thus, may include configuring coil 286 so that it extends over body portion 282 and terminates adjacent should region 290. This can occur by configuring coil 286 prior to, during, or after attaching cap 274 to core wire 172. Alternatively, tip portion 284 can be attached to coil 286 and body portion 282 after coupling cap 274 to enlarged section 180.
It should be understood that this disclosure is, in many respects, only illustrative. Changes may be made in details, particularly in matters of shape, size, and arrangement of steps without exceeding the scope of the invention. The scope of the invention is, of course, defined in the language in which the appended claims are expressed.

Claims (39)

1. An elongate medical device comprising:
an elongate shaft having a distal end and a proximal end; and a distal cap that is formed independently of the elongate shaft, the distal cap having a distal end and a proximal end, the proximal end of the distal cap comprising an aperture configured to accept the distal end of the elongate shaft;
wherein the distal cap is secured to the distal end of the elongate shaft.
2. The elongate medical device of claim 1, wherein the medical device comprises a guidewire, the elongate shaft comprises a core wire having a distal end and a proximal end, the aperture defined in the proximal end of the distal cap is adapted to accept the distal end of the core wire, and the distal cap is formed independently of the core wire and is subsequently attached to the distal end of the core wire.
3. The elongate medical device of claim 1 or 2, wherein the distal cap is secured to the distal end of the elongate shaft via welding.
4. The elongate medical device of claim 1, 2, or 3, wherein the distal cap is laser welded or plasma welded to the distal end of the elongate shaft.
5. The elongate medical device of any of claims 1-4, wherein the elongate shaft comprises a metallic material and the distal cap comprises a metallic material that is welding-compatible with the elongate shaft.
6. The elongate medical device of any of claims 1-5, wherein the proximal end of the distal cap has a substantially cylindrical outer profile and an inner profile that mirrors an outer profile of the distal end of the elongate shaft.
7. The elongate medical device of any of claims 1-6, wherein the distal end of the distal cap is adapted and configured to provide an atraumatic tip to the elongate medical device.
8. The elongate medical device of any of claims 1-7, wherein the proximal end of the distal cap has a hemispherical profile.
9. The elongate medical device of any of claims 1-8, wherein the proximal end of the distal cap is adapted and configured to fit tightly over the distal end of the elongate shaft.
10. The elongate medical device of any of claims 1-9, further comprising a distal sleeve positioned between the distal end of the elongate shaft and an inner surface of the distal cap.
11. The elongate medical device of claim 10, wherein the distal sleeve is secured to the distal end of the elongate shaft and the distal cap is secured to the distal sleeve.
12. The elongate medical device of claim 11, wherein the distal cap is secured to the distal sleeve via either laser welding or plasma welding.
13. The elongate medical device of any of claims 10-12, wherein the distal cap comprises a metallic material that is welding-compatible with the distal sleeve and the elongate shaft, each of which also comprise a metallic material.
14. The elongate medical device of claim 1, wherein the elongate medical device comprises a guidewire.
15. The elongate medical device of any of claims 1-14, wherein the distal cap is formed by one of deep drawing, roll forming or stamping.
16. The elongate medical device of claim 2, wherein the core wire comprises a proximal portion having a first diameter, an intermediate portion having a second diameter that is less than the first diameter, and a distal portion having a diameter that is less than the second diameter.
17. The elongate medical device of claim 16, further comprising a proximal transition region positioned between the proximal portion and the intermediate portion and a distal transition region positioned between the intermediate portion and the distal portion.
18. The elongate medical device of claim 17, further comprising a coil disposed at least partially about the shaft, the coil having a distal end and a proximal end, wherein the proximal end of the coil is positioned proximate the proximal transition region and the distal end of the coil is positioned proximate the distal portion of the core wire.
19. The elongate medical device of claim 17, wherein the proximal end of the coil is positioned proximate the distal transition region and the distal end of the coil is positioned proximate the distal portion of the core wire.
20. The elongate medical device of claim 18 or 19, further comprising a polymeric sleeve positioned over the coil, the polymeric sleeve optionally extending from the proximal transition region to a position proximate the distal portion of the core wire.
21. The elongate medical device of any of claims 1-17, further comprising a coil disposed at least partially about the shaft.
22. The elongate medical device of any of claims 18-21, wherein the distal end of the coil extends distally to a position proximal of the distal end of the shaft, and the proximal end of the distal cap extends proximally to the same position.
23. The elongate medical device of any of claims 18-22, wherein the distal cap, the distal end of the coil and the distal end of the shaft are attached via welding.
24. The elongate medical device of claim 2, wherein the core wire further comprises a distal heat sink portion that is positioned distal of the distal portion and that has a diameter that is greater than that of the distal portion.
25. The elongate medical device of claim 24, wherein the proximal end of the distal cap is adapted and configured to fit tightly over a distal end of the distal heat sink portion and extends proximally to an intermediate position on the distal heat sink portion.
26. The elongate medical device of any of claims 1-25 produced by a process of:
providing the elongate shaft having the distal end and the proximal end;
providing the distal cap formed independently of the elongate shaft, the distal cap including the distal end and the proximal end, the proximal end of the distal cap comprising the aperture configured to accept the distal end of the elongate shaft;
positioning the distal cap over the distal end of the elongate shaft by inserting the distal end of the elongate shaft into the distal cap aperture; and securing the distal cap to the distal end of the elongate shaft.
27. The elongate medical device comprising the guidewire of claim 2 produced by a process of:
providing the core wire having the distal end and the proximal end;
providing the distal cap formed independently of the core wire, the distal cap having the distal end and the proximal end, the proximal end of the distal cap comprising the aperture configured to fit over the distal end of the core wire;
inserting the distal end of the core wire into the distal cap aperture; and securing the distal cap over the distal end of the core wire.
28. A method of producing the elongate medical device of any of claims 1-25, the method comprising:
providing the distal cap formed independently of the elongate shaft, the distal cap including the distal end and the proximal end, the proximal end of the distal cap comprising the aperture configured to fit over the distal end of the elongate shaft;
positioning the distal cap over the distal end of the elongate shaft by inserting the distal end of the elongate shaft into the distal cap aperture; and securing the distal cap to the distal end of the elongate shaft.
29. A method of producing the elongate medical device comprising a guidewire of claim 2, the method comprising:
providing the core wire having the distal end and the proximal end;
providing the distal cap formed independently of the core wire, the distal cap having the distal end and the proximal end, the proximal end of the distal cap comprising the aperture configured to fit over the distal end of the core wire;
inserting the distal end of the core wire into the aperture in the distal cap;
and securing the distal cap over the distal end of the core wire.
30. The method of claim 29, further comprising positioning a coil having a distal end and a proximal end, where the distal end of the coil is positioned proximate the distal portion of the core wire.
31. The method of claim 30, wherein the distal end of the coil extends distally to a position proximal of the distal end of the core wire, and the proximal end of the distal cap extends proximally to the same position.
32. The method of claim 31, wherein the distal cap, the distal end of the coil and the distal end of the core wire are attached via welding.
33. The method of any of claims 28-32, wherein the distal cap is formed via injection molding.
34. The method of any of claims 28-33, wherein securing the distal cap comprises melting at least part of the distal cap via laser or plasma welding.
35. The elongate medical device of claim 1, wherein the medical device comprises a guidewire, the elongate shaft comprises a core wire having a distal end and a proximal end, the distal cap having the distal end and the proximal end, the proximal end including a tubular structure defining a lumen defining the aperture, the lumen configured to fit over the distal end of the core wire, the distal end of the distal cap defining an arcuate atraumatic surface, wherein the distal cap is attached to the distal end of the core wire by inserting the distal end of the core wire into the lumen and welding the distal cap to the core wire.
36. A method of producing the guidewire of claim 35, the method comprising:
providing the core wire having the distal end and the proximal end;
providing the tubular structure having a distal end and a proximal end;
positioning the tubular structure over the distal end of the core wire;
positioning a metal ball proximate the distal end of the tubular sleeve; and melting at least a portion of the tubular sleeve and the metal ball via laser or plasma welding to form the arcuate atraumatic surface.
37. The method of claim 36, further comprising positioning a coil over the distal end of the core wire prior to melting the tubular sleeve and the metal ball.
38. A method of manufacturing the elongate medical device of claim 1, the method comprising:
providing the elongated shaft having the proximal end and the distal end;
providing a tubular member having a proximal portion and a distal portion;
attaching a tip to the distal portion of the tubular member to form the distal cap member comprising the tubular member and the tip; and coupling the proximal portion of the tubular body to the distal end of the shaft.
39. A guidewire comprising:
a core wire having a distal end and a proximal end; and means of forming a distal tip, said means formed independently and then subsequently secured to the distal end of the core wire.
CA002515145A 2003-02-26 2004-02-24 Elongate medical device with distal cap Abandoned CA2515145A1 (en)

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US10/375,207 US7169118B2 (en) 2003-02-26 2003-02-26 Elongate medical device with distal cap
US10/375,207 2003-02-26
PCT/US2004/005439 WO2004075950A2 (en) 2003-02-26 2004-02-24 Elongate medical device with distal cap

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JP (1) JP4805138B2 (en)
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Families Citing this family (104)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6554942B2 (en) * 2000-12-28 2003-04-29 Scimed Life Systems, Inc. Method of manufacturing a guidewire with an extrusion jacket
ATE347393T1 (en) 2001-07-05 2006-12-15 Precision Vascular Systems Inc MEDICAL DEVICE HAVING A TORQUE-TRANSMITTING SOFT END PIECE AND METHOD FOR SHAPING IT
US7914467B2 (en) 2002-07-25 2011-03-29 Boston Scientific Scimed, Inc. Tubular member having tapered transition for use in a medical device
US8377035B2 (en) * 2003-01-17 2013-02-19 Boston Scientific Scimed, Inc. Unbalanced reinforcement members for medical device
US7824345B2 (en) 2003-12-22 2010-11-02 Boston Scientific Scimed, Inc. Medical device with push force limiter
JP3810413B2 (en) * 2004-03-29 2006-08-16 朝日インテック株式会社 Medical guidewire
US7819887B2 (en) 2004-11-17 2010-10-26 Rex Medical, L.P. Rotational thrombectomy wire
EP1767239B1 (en) * 2005-09-27 2008-12-10 Asahi Intecc Co., Ltd. A medical guide wire
US7749265B2 (en) * 2005-10-05 2010-07-06 Kenergy, Inc. Radio frequency antenna for a wireless intravascular medical device
US20070083132A1 (en) * 2005-10-11 2007-04-12 Sharrow James S Medical device coil
US7850623B2 (en) 2005-10-27 2010-12-14 Boston Scientific Scimed, Inc. Elongate medical device with continuous reinforcement member
US8235916B2 (en) * 2006-02-03 2012-08-07 Pacesetter, Inc. System and method for manipulating insertion pathways for accessing target sites
US7846361B2 (en) 2006-07-20 2010-12-07 Orbusneich Medical, Inc. Bioabsorbable polymeric composition for a medical device
US8551020B2 (en) 2006-09-13 2013-10-08 Boston Scientific Scimed, Inc. Crossing guidewire
DE102006047675A1 (en) * 2006-09-28 2008-04-03 Epflex Feinwerktechnik Gmbh Guidewire with core and distal sheath
US7959942B2 (en) 2006-10-20 2011-06-14 Orbusneich Medical, Inc. Bioabsorbable medical device with coating
CN103212115B (en) 2006-10-20 2016-09-14 奥巴斯尼茨医学公司 Bioabsorbable polymer composition and armarium
JP5214878B2 (en) * 2006-12-28 2013-06-19 テルモ株式会社 Guide wire
US8308658B2 (en) 2007-04-13 2012-11-13 Neometrics, Inc. Medical guidewire
US20080306453A1 (en) * 2007-06-06 2008-12-11 Cook Incorporated Coupling wire guide and method for making same
US8409114B2 (en) 2007-08-02 2013-04-02 Boston Scientific Scimed, Inc. Composite elongate medical device including distal tubular member
US8105246B2 (en) 2007-08-03 2012-01-31 Boston Scientific Scimed, Inc. Elongate medical device having enhanced torque and methods thereof
US8821477B2 (en) 2007-08-06 2014-09-02 Boston Scientific Scimed, Inc. Alternative micromachined structures
US9808595B2 (en) 2007-08-07 2017-11-07 Boston Scientific Scimed, Inc Microfabricated catheter with improved bonding structure
IL194805A0 (en) * 2007-10-29 2009-08-03 Lifescan Inc Medical device flexible conduit and method of manufacture
CA2641699A1 (en) * 2007-10-30 2009-04-30 Lifescan, Inc. Method for inserting a medical device flexible conduit into a user's target site
US7841994B2 (en) 2007-11-02 2010-11-30 Boston Scientific Scimed, Inc. Medical device for crossing an occlusion in a vessel
US20090177119A1 (en) * 2008-01-03 2009-07-09 Boston Scientific Scimed, Inc. Articulating intracorporeal medical device
US9095685B2 (en) * 2008-01-23 2015-08-04 Mediguide Ltd. Sensor mounted flexible guidewire
US8343076B2 (en) * 2008-01-23 2013-01-01 MediGuide, Ltd. Sensor mounted flexible guidewire
US8376961B2 (en) 2008-04-07 2013-02-19 Boston Scientific Scimed, Inc. Micromachined composite guidewire structure with anisotropic bending properties
US20090275862A1 (en) * 2008-04-30 2009-11-05 Cook Incorporated Guidewire and method of making same
US20090287145A1 (en) * 2008-05-15 2009-11-19 Altura Interventional, Inc. Devices and methods for treatment of abdominal aortic aneurysms
US8002715B2 (en) * 2008-05-30 2011-08-23 Boston Scientific Scimed, Inc. Medical device including a polymer sleeve and a coil wound into the polymer sleeve
US20100022989A1 (en) * 2008-07-25 2010-01-28 Parasmo Ronald S Steerable catheter and method of making the same
US8535243B2 (en) 2008-09-10 2013-09-17 Boston Scientific Scimed, Inc. Medical devices and tapered tubular members for use in medical devices
US20100063479A1 (en) * 2008-09-10 2010-03-11 Boston Scientific Scimed, Inc. Small profile, tubular component design and method of manufacture
US8795254B2 (en) * 2008-12-10 2014-08-05 Boston Scientific Scimed, Inc. Medical devices with a slotted tubular member having improved stress distribution
JP4913198B2 (en) * 2009-10-27 2012-04-11 株式会社パテントストラ Medical guide wire, method for manufacturing medical guide wire, assembly of medical guide wire, microcatheter and guiding catheter, and assembly of medical guide wire, balloon catheter and guiding catheter
US8137293B2 (en) 2009-11-17 2012-03-20 Boston Scientific Scimed, Inc. Guidewires including a porous nickel-titanium alloy
EP2559403B1 (en) * 2009-12-01 2016-05-04 Altura Medical, Inc. Modular endograft devices
JP5146970B2 (en) * 2010-01-21 2013-02-20 朝日インテック株式会社 Medical guidewire
WO2011123689A1 (en) 2010-03-31 2011-10-06 Boston Scientific Scimed, Inc. Guidewire with a flexural rigidity profile
US9795406B2 (en) 2010-05-13 2017-10-24 Rex Medical, L.P. Rotational thrombectomy wire
US9023070B2 (en) 2010-05-13 2015-05-05 Rex Medical, L.P. Rotational thrombectomy wire coupler
US8764779B2 (en) 2010-05-13 2014-07-01 Rex Medical, L.P. Rotational thrombectomy wire
US8663259B2 (en) 2010-05-13 2014-03-04 Rex Medical L.P. Rotational thrombectomy wire
WO2012040240A1 (en) 2010-09-20 2012-03-29 Altura Medical, Inc. Stent graft delivery systems and associated methods
EP2621335B1 (en) * 2010-09-29 2015-11-18 St. Jude Medical Coordination Center BVBA Sensor guide wire
US11298251B2 (en) 2010-11-17 2022-04-12 Abbott Cardiovascular Systems, Inc. Radiopaque intraluminal stents comprising cobalt-based alloys with primarily single-phase supersaturated tungsten content
JP5382953B2 (en) * 2011-01-28 2014-01-08 朝日インテック株式会社 Guide wire
US8795202B2 (en) 2011-02-04 2014-08-05 Boston Scientific Scimed, Inc. Guidewires and methods for making and using the same
US9072874B2 (en) 2011-05-13 2015-07-07 Boston Scientific Scimed, Inc. Medical devices with a heat transfer region and a heat sink region and methods for manufacturing medical devices
US9724494B2 (en) 2011-06-29 2017-08-08 Abbott Cardiovascular Systems, Inc. Guide wire device including a solderable linear elastic nickel-titanium distal end section and methods of preparation therefor
US20130110000A1 (en) * 2011-10-31 2013-05-02 Terumo Medical Corporation Dual Diameter Introducer Guide Wire
US20130190772A1 (en) * 2012-01-24 2013-07-25 Mis Surgical, Llc Elastic Guide Wire for Spinal Surgery
CN104185490B (en) * 2012-01-31 2017-10-20 波士顿科学西美德公司 Guiding extension conduit
WO2013179103A1 (en) * 2012-05-31 2013-12-05 Baylis Medical Inc. Radiofrequency perforation apparatus
AU2013299425A1 (en) 2012-08-10 2015-03-19 Altura Medical, Inc. Stent delivery systems and associated methods
EP2922593B1 (en) * 2012-11-21 2020-04-08 Concert Medical, LLC Preformed guidewire
JP5780525B2 (en) * 2012-12-06 2015-09-16 朝日インテック株式会社 Guide wire
US9498356B2 (en) 2012-12-19 2016-11-22 Cook Medical Technologies, LLC Flexible stent and delivery system
EP2967340A1 (en) 2013-03-13 2016-01-20 St. Jude Medical Coordination Center BVBA Sensor guide wire with shape memory tip
WO2014144809A1 (en) 2013-03-15 2014-09-18 Altura Medical, Inc. Endograft device delivery systems and associated methods
US10835183B2 (en) * 2013-07-01 2020-11-17 Zurich Medical Corporation Apparatus and method for intravascular measurements
USD766433S1 (en) 2013-11-04 2016-09-13 Cardiovascular Systems, Inc. Eccentric crown
MX2016014146A (en) 2014-04-29 2017-02-06 Bard Inc C R Kink-resistant guidewire with improved rigidity.
US10391282B2 (en) 2014-07-08 2019-08-27 Teleflex Innovations S.À.R.L. Guidewires and methods for percutaneous occlusion crossing
US9763814B2 (en) 2014-10-24 2017-09-19 Cook Medical Technologies Llc Elongate medical device
US10179225B2 (en) 2015-02-27 2019-01-15 Thomas A. Sos Atraumatic micropuncture guidewire and guidewire extension
US9768664B2 (en) 2015-05-21 2017-09-19 The Boeing Company Balanced eccentric gear design and method
US10596353B2 (en) * 2015-10-15 2020-03-24 MRI Interventions, Inc. MRI-compatible guidewire
US10203022B2 (en) 2015-11-04 2019-02-12 The Boeing Company Elliptically interfacing wobble motion gearing system and method
US10024391B2 (en) 2016-01-06 2018-07-17 The Boeing Company Elliptically interfacing gearbox
EP3248644B1 (en) * 2016-03-10 2020-08-12 Asahi Intecc Co., Ltd. Guide wire
US10792473B2 (en) 2016-03-16 2020-10-06 St. Jude Medical Coordination Center Bvba Core wire having a flattened portion to provide preferential bending
US10574109B2 (en) 2016-04-28 2020-02-25 The Boeing Company Permanent magnet biased virtual elliptical motor
EP3518728B1 (en) 2016-09-30 2021-10-27 Ambu A/S An endoscope
EP3528885B1 (en) 2016-10-18 2024-03-13 Boston Scientific Scimed Inc. Guide extension catheter
US10603472B2 (en) * 2016-10-25 2020-03-31 Biosense Webster (Israel) Ltd. Guidewires having improved mechanical strength and electromagnetic shielding
CN110177594B (en) 2016-11-22 2022-07-29 波士顿科学国际有限公司 Compression and/or tension resistant medical device shaft
DK3551271T3 (en) 2016-12-08 2023-10-02 Abiomed Inc OVERMOLDING TECHNIQUE FOR DESIGNING PEEL-AWAY INTRODUCING
US10953204B2 (en) 2017-01-09 2021-03-23 Boston Scientific Scimed, Inc. Guidewire with tactile feel
US10215244B2 (en) 2017-03-02 2019-02-26 The Boeing Company Elliptically interfacing gear assisted braking system
CN110430843B (en) 2017-03-14 2022-06-07 波士顿科学国际有限公司 Medical device shaft including a liner
JP6854356B2 (en) 2017-03-14 2021-04-07 ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. Systems that deliver implantable medical devices and systems that implant heart valves
US10520063B2 (en) 2017-04-21 2019-12-31 The Boeing Company Mechanical virtual elliptical drive
CN110573099B (en) 2017-05-03 2023-01-03 美敦力瓦斯科尔勒公司 Tissue removal catheter
US11690645B2 (en) 2017-05-03 2023-07-04 Medtronic Vascular, Inc. Tissue-removing catheter
US10267383B2 (en) 2017-05-03 2019-04-23 The Boeing Company Self-aligning virtual elliptical drive
CN110868965B (en) 2017-05-03 2021-12-28 波士顿科学国际有限公司 Medical device with sealing assembly
WO2019083757A1 (en) 2017-10-26 2019-05-02 Teleflex Innovations S.A.R.L. Subintimal catheter device and assembly
WO2019109063A2 (en) 2017-12-03 2019-06-06 Paul Ram H Jr Mri compatible interventional wireguide
EP3784177A1 (en) 2018-04-26 2021-03-03 Boston Scientific Scimed, Inc. Motorized telescoping medical device delivery system
WO2019210165A1 (en) 2018-04-26 2019-10-31 Boston Scientific Scimed, Inc. Medical device with coupling member
WO2019210158A1 (en) 2018-04-26 2019-10-31 Boston Scientific Scimed, Inc. Medical device with telescoping sealing assembly
CA3100259A1 (en) 2018-05-16 2019-11-21 Abiomed, Inc. Peel-away sheath assembly
US11357534B2 (en) 2018-11-16 2022-06-14 Medtronic Vascular, Inc. Catheter
US10968969B2 (en) 2019-03-18 2021-04-06 The Boeing Company Nutational braking systems and methods
US11819236B2 (en) 2019-05-17 2023-11-21 Medtronic Vascular, Inc. Tissue-removing catheter
WO2021030567A1 (en) 2019-08-15 2021-02-18 Boston Scientific Scimed, Inc. Medical device including attachable tip member
US20220401706A1 (en) * 2019-10-16 2022-12-22 Embrace Medical Ltd Guidewire with elastically articulatable tip
US11459098B2 (en) 2019-11-27 2022-10-04 The Boeing Company Variable speed transmission and related methods
CN114901340A (en) * 2020-10-01 2022-08-12 泰利福医疗公司 Probe with improved threading capability

Family Cites Families (345)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1553227A (en) 1924-09-18 1925-09-08 Paragon Button Corp Slicing machine
US1866888A (en) 1931-03-11 1932-07-12 Master Woodworker Mfg Co Sawing machine
US2275827A (en) 1940-07-02 1942-03-10 Belmont Radio Corp Electric motor
US2441166A (en) 1942-03-27 1948-05-11 Raspet August Helical spring
US2413805A (en) 1943-08-17 1947-01-07 Theodore W Vickers Electrical machine
US2561890A (en) 1945-07-25 1951-07-24 George C Stoddard Dynamoelectric machine
US2722614A (en) 1951-08-11 1955-11-01 Gulton Mfg Co Vibration and shock-responsive device
US2857536A (en) 1955-07-18 1958-10-21 Edward C Light Variable reluctance machine
US2864017A (en) 1955-11-28 1958-12-09 Waltscheff Dimo Dimitroff Inducto-motive power apparatus with a plurality of rotors
US2871793A (en) 1956-06-29 1959-02-03 Robbins & Myers Electric motor and pump combination
US3249776A (en) 1962-06-13 1966-05-03 Bendix Corp Nutation motor
US3294994A (en) 1963-05-10 1966-12-27 Bendix Corp Nutation motor or generator
US3363470A (en) 1964-07-20 1968-01-16 Raphael O. Yavne Accelerometer
US3334253A (en) 1966-04-25 1967-08-01 Francis A Hill Magnet traction motors
US3452740A (en) 1966-05-31 1969-07-01 Us Catheter & Instr Corp Spring guide manipulator
US3452227A (en) 1966-10-21 1969-06-24 Elvin C Welch Motor with gyrating rotor
GB1169984A (en) 1967-01-25 1969-11-12 Nat Res Dev Improvements relating to Dynamo Electric Machines
US3463953A (en) 1967-03-20 1969-08-26 Gilbert A Maxwell Resonant motor
US3512019A (en) 1968-02-21 1970-05-12 Systems Technology Inc Electromagnetic device
US3625200A (en) 1969-08-26 1971-12-07 Us Catheter & Instr Corp Controlled curvable tip member
US3686990A (en) 1970-03-05 1972-08-29 Geometron Co Inc Cutting elongated stock
US3824368A (en) * 1971-12-30 1974-07-16 Avco Corp Laser welding
SU712908A1 (en) 1973-07-16 1980-01-30 Amdurov Aleksandr E End-face wave-type electric motor
US3841308A (en) 1973-10-15 1974-10-15 Medical Evaluation Devices & I Distally valved catheter device
US3890977A (en) 1974-03-01 1975-06-24 Bruce C Wilson Kinetic memory electrodes, catheters and cannulae
CS171544B1 (en) 1974-09-03 1976-10-29
US3906938A (en) 1974-09-03 1975-09-23 Lake Region Manufacturing Comp Coil spring wire guide
US4003369A (en) 1975-04-22 1977-01-18 Medrad, Inc. Angiographic guidewire with safety core wire
US4020829A (en) 1975-10-23 1977-05-03 Willson James K V Spring guide wire with torque control for catheterization of blood vessels and method of using same
US4000672A (en) 1976-02-26 1977-01-04 Altair National Corporation Slitting machine for corrugated pipe
US4142119A (en) 1977-03-21 1979-02-27 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Rotary electric device
SU758421A1 (en) 1978-05-04 1980-08-23 Московский Ордена Ленина Авиационный Институт Им.Серго Орджоникидзе Motor-vibrator with rolling rotor
US4215703A (en) 1978-08-29 1980-08-05 Willson James K V Variable stiffness guide wire
US4330725A (en) 1980-03-10 1982-05-18 Morgan Actuators, Inc. Nutating motor coupling
DE3029907A1 (en) 1980-08-07 1982-03-18 Hoechst Ag, 6000 Frankfurt CONTINUOUS METHOD AND DEVICE FOR PRODUCING A VINYL CHLORIDE POLYMERISATE IN AQUEOUS SUSPENSION
EP0069522A1 (en) 1981-06-26 1983-01-12 Research Machines Plc Educational aid for teaching computer programming
US4425919A (en) 1981-07-27 1984-01-17 Raychem Corporation Torque transmitting catheter apparatus
FR2515859A1 (en) 1981-10-29 1983-05-06 Crouzet Sa ELECTROMAGNETIC CYLINDER DEBRAYABLE
US4476754A (en) 1981-12-07 1984-10-16 Ducret Lucien C Automatic cable measuring and cutting machine
AU550184B2 (en) 1982-02-26 1986-03-06 Unilever Plc Pack for detergent powder
US4545390A (en) 1982-09-22 1985-10-08 C. R. Bard, Inc. Steerable guide wire for balloon dilatation procedure
DE3245958A1 (en) 1982-12-11 1984-06-14 Battelle-Institut E.V., 6000 Frankfurt LASER ARRANGEMENT
US4563181A (en) 1983-02-18 1986-01-07 Mallinckrodt, Inc. Fused flexible tip catheter
FR2541775B1 (en) 1983-02-28 1985-10-04 Onera (Off Nat Aerospatiale) ELECTROSTATIC SUSPENSION ACCELEROMETERS
US4774949A (en) 1983-06-14 1988-10-04 Fogarty Thomas J Deflector guiding catheter
US4665906A (en) 1983-10-14 1987-05-19 Raychem Corporation Medical devices incorporating sim alloy elements
US4538622A (en) * 1983-11-10 1985-09-03 Advanced Cardiovascular Systems, Inc. Guide wire for catheters
US4574670A (en) 1983-11-17 1986-03-11 Lockheed Corporation Multiple angle cutting apparatus
US5135531A (en) 1984-05-14 1992-08-04 Surgical Systems & Instruments, Inc. Guided atherectomy system
US4781186A (en) 1984-05-30 1988-11-01 Devices For Vascular Intervention, Inc. Atherectomy device having a flexible housing
US4786220A (en) 1984-06-18 1988-11-22 Borg-Warner Corporation Cutting tool wear monitor
US4580551A (en) 1984-11-02 1986-04-08 Warner-Lambert Technologies, Inc. Flexible plastic tube for endoscopes and the like
JPS61110198A (en) 1984-11-05 1986-05-28 株式会社東芝 Matrix type display unit
US5470330A (en) 1984-12-07 1995-11-28 Advanced Interventional Systems, Inc. Guidance and delivery system for high-energy pulsed laser light
DE3447642C1 (en) 1984-12-28 1986-09-18 Bernhard M. Dr. 5600 Wuppertal Cramer Steerable guidewire for catheters
US4682607A (en) * 1985-12-02 1987-07-28 Vlv Associates Wire guide
JPH025799Y2 (en) 1986-02-07 1990-02-13
US4721117A (en) 1986-04-25 1988-01-26 Advanced Cardiovascular Systems, Inc. Torsionally stabilized guide wire with outer jacket
US4867173A (en) 1986-06-30 1989-09-19 Meadox Surgimed A/S Steerable guidewire
US4922777A (en) 1986-09-05 1990-05-08 Contour Saws, Inc. Band saw for cutting shaped pieces of bar stock
US4719924A (en) * 1986-09-09 1988-01-19 C. R. Bard, Inc. Small diameter steerable guidewire with adjustable tip
DE3633691C1 (en) 1986-10-03 1987-07-23 Keuro Maschb Gmbh & Co Kg Device for feeding rod-shaped workpiece material in a cutting machine
US4790331A (en) 1986-12-02 1988-12-13 Sherwood Medical Company Method for placement of catheter in a blood vessel
US4763647A (en) 1987-01-06 1988-08-16 C. R. Bard, Inc. Dual coil steerable guidewire
JPH0685927B2 (en) 1987-01-30 1994-11-02 株式会社エフイ−シ− Drive device for vertical axis rolling mill
US5250069A (en) 1987-02-27 1993-10-05 Terumo Kabushiki Kaisha Catheter equipped with expansible member and production method thereof
US4811743A (en) 1987-04-21 1989-03-14 Cordis Corporation Catheter guidewire
US5211183A (en) 1987-05-13 1993-05-18 Wilson Bruce C Steerable memory alloy guide wires
US4989608A (en) 1987-07-02 1991-02-05 Ratner Adam V Device construction and method facilitating magnetic resonance imaging of foreign objects in a body
SU1529365A1 (en) 1987-08-13 1989-12-15 Всесоюзный научно-исследовательский институт электромеханики Stepping electric motor with rolling rotor
US4875489A (en) 1987-08-14 1989-10-24 Advanced Cardiovascular Systems, Inc. Extendable guidewire
US5181668A (en) 1987-09-07 1993-01-26 Osaka Gas Co., Ltd. Apparatus for running a wire through a pipe
US4846193A (en) 1987-09-21 1989-07-11 Advanced Cardiovascular Systems, Inc. Extendable guide wire for vascular procedures
US4953553A (en) 1989-05-11 1990-09-04 Advanced Cardiovascular Systems, Inc. Pressure monitoring guidewire with a flexible distal portion
US4964409A (en) 1989-05-11 1990-10-23 Advanced Cardiovascular Systems, Inc. Flexible hollow guiding member with means for fluid communication therethrough
US5050606A (en) 1987-09-30 1991-09-24 Advanced Cardiovascular Systems, Inc. Method for measuring pressure within a patient's coronary artery
US5273042A (en) 1987-10-28 1993-12-28 Medical Parameters, Inc. Guidewire advancement method
US4934380A (en) 1987-11-27 1990-06-19 Boston Scientific Corporation Medical guidewire
US4832047A (en) 1987-12-15 1989-05-23 Target Therapeutics Guide wire device
US5009137A (en) 1987-12-18 1991-04-23 Pitney Bowes Inc. Cutter module for a modular mailing machine
US4827941A (en) 1987-12-23 1989-05-09 Advanced Cardiovascular Systems, Inc. Extendable guidewire for cardiovascular procedures
US4846186A (en) 1988-01-12 1989-07-11 Cordis Corporation Flexible guidewire
DE3801514A1 (en) 1988-01-20 1989-08-03 Schmidt Feinmech ACCELERATION SENSOR AND METHOD FOR THE PRODUCTION THEREOF
DE3903133A1 (en) 1988-02-04 1989-08-31 Amada Co WORKPIECE WORKABILITY DETECTION METHOD AND METHOD FOR MACHINING A WORKPIECE BY MEANS OF A CHIP MACHINING MACHINE USING THIS METHOD
US4884579A (en) 1988-04-18 1989-12-05 Target Therapeutics Catheter guide wire
US4935017A (en) 1988-04-29 1990-06-19 C. R. Bard, Inc. Variable shaped catheter system and method for catheterization
US4998923A (en) 1988-08-11 1991-03-12 Advanced Cardiovascular Systems, Inc. Steerable dilatation catheter
US4917102A (en) 1988-09-14 1990-04-17 Advanced Cardiovascular Systems, Inc. Guidewire assembly with steerable adjustable tip
US4950257A (en) 1988-09-15 1990-08-21 Mallinckrodt, Inc. Catheter introducer with flexible tip
US4922164A (en) 1988-10-03 1990-05-01 Sarcos Group Eccentric motion motor
US4994069A (en) 1988-11-02 1991-02-19 Target Therapeutics Vaso-occlusion coil and method
US5507751A (en) 1988-11-09 1996-04-16 Cook Pacemaker Corporation Locally flexible dilator sheath
US4985022A (en) 1988-11-23 1991-01-15 Med Institute, Inc. Catheter having durable and flexible segments
US4932959A (en) 1988-12-01 1990-06-12 Advanced Cardiovascular Systems, Inc. Vascular catheter with releasably secured guidewire
US5372587A (en) * 1989-01-09 1994-12-13 Pilot Cariovascular Systems, Inc. Steerable medical device
US5007434A (en) 1989-02-07 1991-04-16 Advanced Cardiovascular Systems, Inc. Catheter tip attitude controlling guide wire
US4966163A (en) 1989-02-14 1990-10-30 Advanced Cardiovascular Systems, Inc. Extendable guidewire for vascular procedures
US5052404A (en) 1989-03-02 1991-10-01 The Microspring Company, Inc. Torque transmitter
US4911148A (en) 1989-03-14 1990-03-27 Intramed Laboratories, Inc. Deflectable-end endoscope with detachable flexible shaft assembly
US4960410A (en) 1989-03-31 1990-10-02 Cordis Corporation Flexible tubular member for catheter construction
CA2030786C (en) 1989-04-13 1997-04-01 Atsushi Utsumi Catheter
JPH02295569A (en) * 1989-04-25 1990-12-06 C R Bard Inc Guide wire
US5063935A (en) 1989-04-27 1991-11-12 C. R. Bard, Inc. Catheter guidewire with varying radiopacity
US4955384A (en) 1989-05-11 1990-09-11 Advanced Cardiovascular Systems, Inc. Guiding member for vascular catheters with a flexible link distal section
US4955862A (en) 1989-05-22 1990-09-11 Target Therapeutics, Inc. Catheter and catheter/guide wire device
US4954022A (en) 1989-06-16 1990-09-04 Underwood Mold Co., Inc. Method for machining multiple cuts in a workpiece to a uniform depth
US4968306A (en) 1989-07-07 1990-11-06 Advanced Cardiovascular Systems, Inc. Intravascular catheter having an adjustable length infusion section to delivery therapeutic fluid
US5144959A (en) 1989-08-15 1992-09-08 C. R. Bard, Inc. Catheter guidewire with varying radiopacity
US5256144A (en) 1989-11-02 1993-10-26 Danforth Biomedical, Inc. Low profile, high performance interventional catheters
US5095915A (en) 1990-03-19 1992-03-17 Target Therapeutics Guidewire with flexible distal tip
US4990143A (en) 1990-04-09 1991-02-05 Sheridan Catheter Corporation Reinforced medico-surgical tubes
US5109830A (en) 1990-04-10 1992-05-05 Candela Laser Corporation Apparatus for navigation of body cavities
US5238004A (en) * 1990-04-10 1993-08-24 Boston Scientific Corporation High elongation linear elastic guidewire
US5059177A (en) 1990-04-19 1991-10-22 Cordis Corporation Triple lumen balloon catheter
US5135503A (en) * 1990-05-16 1992-08-04 Advanced Cardiovascular Systems, Inc. Shaping ribbon for guiding members
US5147317A (en) 1990-06-04 1992-09-15 C.R. Bard, Inc. Low friction varied radiopacity guidewire
US5040543A (en) 1990-07-25 1991-08-20 C. R. Bard, Inc. Movable core guidewire
US5345945A (en) 1990-08-29 1994-09-13 Baxter International Inc. Dual coil guidewire with radiopaque distal tip
US5125395A (en) 1990-09-12 1992-06-30 Adair Edwin Lloyd Deflectable sheath for optical catheter
US5267979A (en) 1990-09-17 1993-12-07 E-Z-Em, Inc. Pressure responsive valve catheter
EP0491349B1 (en) 1990-12-18 1998-03-18 Advanced Cardiovascular Systems, Inc. Method of manufacturing a Superelastic guiding member
US5341818A (en) 1992-12-22 1994-08-30 Advanced Cardiovascular Systems, Inc. Guidewire with superelastic distal portion
US6165292A (en) 1990-12-18 2000-12-26 Advanced Cardiovascular Systems, Inc. Superelastic guiding member
US5106455A (en) 1991-01-28 1992-04-21 Sarcos Group Method and apparatus for fabrication of micro-structures using non-planar, exposure beam lithography
US5329923A (en) 1991-02-15 1994-07-19 Lundquist Ingemar H Torquable catheter
US5228441A (en) 1991-02-15 1993-07-20 Lundquist Ingemar H Torquable catheter and method
US5231989A (en) 1991-02-15 1993-08-03 Raychem Corporation Steerable cannula
US5454787A (en) 1991-02-15 1995-10-03 Lundquist; Ingemar H. Torquable tubular assembly and torquable catheter utilizing the same
US5315996A (en) 1991-02-15 1994-05-31 Lundquist Ingemar H Torquable catheter and method
AU660444B2 (en) 1991-02-15 1995-06-29 Ingemar H. Lundquist Torquable catheter and method
US5254107A (en) 1991-03-06 1993-10-19 Cordis Corporation Catheter having extended braid reinforced transitional tip
ATE221795T1 (en) 1991-05-07 2002-08-15 Target Therapeutics Inc CATHETER GUIDE WIRE
US5242759A (en) 1991-05-21 1993-09-07 Cook Incorporated Joint, a laminate, and a method of preparing a nickel-titanium alloy member surface for bonding to another layer of metal
US5769830A (en) 1991-06-28 1998-06-23 Cook Incorporated Soft tip guiding catheter
US5304131A (en) 1991-07-15 1994-04-19 Paskar Larry D Catheter
US5306252A (en) 1991-07-18 1994-04-26 Kabushiki Kaisha Kobe Seiko Sho Catheter guide wire and catheter
WO1993001856A1 (en) 1991-07-24 1993-02-04 Advanced Cardiovascular Systems, Inc. Low profile perfusion-type dilatation catheter
US5630806A (en) 1991-08-13 1997-05-20 Hudson International Conductors Spiral wrapped medical tubing
US5741429A (en) 1991-09-05 1998-04-21 Cardia Catheter Company Flexible tubular device for use in medical applications
CA2117088A1 (en) 1991-09-05 1993-03-18 David R. Holmes Flexible tubular device for use in medical applications
US5308435A (en) 1991-10-07 1994-05-03 Home Fashions, Inc. Method and apparatus for fabricating honeycomb insulating material
US5605162A (en) * 1991-10-15 1997-02-25 Advanced Cardiovascular Systems, Inc. Method for using a variable stiffness guidewire
US5376084A (en) 1991-10-17 1994-12-27 Imagyn Medical, Inc. Catheter with internal mandrel and method
US5333620A (en) 1991-10-30 1994-08-02 C. R. Bard, Inc. High performance plastic coated medical guidewire
US5253653A (en) * 1991-10-31 1993-10-19 Boston Scientific Corp. Fluoroscopically viewable guidewire for catheters
US5205830A (en) 1991-11-12 1993-04-27 Arrow International Investment Corporation Catheter assembly
US5243996A (en) * 1992-01-03 1993-09-14 Cook, Incorporated Small-diameter superelastic wire guide
US5465732A (en) * 1992-03-31 1995-11-14 Boston Scientific Corporation Fluoroscopically viewable multifilar calibrated guidewire and method of measuring occlusions with calibrated guidewires
JP3151927B2 (en) 1992-04-10 2001-04-03 株式会社村田製作所 Acceleration sensor
US5254106A (en) 1992-04-17 1993-10-19 Feaster Fred T Hydrodissection needle
US5259393A (en) 1992-05-13 1993-11-09 Cordis Corporation Guidewire having controlled radiopacity tip
US5315906A (en) 1992-05-15 1994-05-31 Vought Aircraft Company Automated extrusion processing machine
US5584821A (en) 1992-06-02 1996-12-17 E-Z-Em, Inc. Soft tip catheter
ATE182273T1 (en) 1992-08-18 1999-08-15 Spectranetics Corp GUIDE WIRE WITH FIBER OPTICS
US5257974A (en) 1992-08-19 1993-11-02 Scimed Life Systems, Inc. Performance enhancement adaptor for intravascular balloon catheter
US5437288A (en) 1992-09-04 1995-08-01 Mayo Foundation For Medical Education And Research Flexible catheter guidewire
US5334145A (en) 1992-09-16 1994-08-02 Lundquist Ingemar H Torquable catheter
US5299580A (en) * 1992-10-09 1994-04-05 Scimed Life Systems, Inc. Guidewire with safety ribbon with substantially axially symmetric flexibility
US5501228A (en) * 1992-10-30 1996-03-26 Scimed Life Systems, Inc. Vibration sensing guide wire
US5441483A (en) 1992-11-16 1995-08-15 Avitall; Boaz Catheter deflection control
AU5672194A (en) 1992-11-18 1994-06-22 Spectrascience, Inc. Apparatus for diagnostic imaging
US5372144A (en) * 1992-12-01 1994-12-13 Scimed Life Systems, Inc. Navigability improved guidewire construction and method of using same
US5476701A (en) 1992-12-20 1995-12-19 Berger; David Table pad construction
US5368564A (en) 1992-12-23 1994-11-29 Angeion Corporation Steerable catheter
JPH06202361A (en) 1992-12-28 1994-07-22 Fuji Xerox Co Ltd Electrophotographic sensitive body and its production
US5669926A (en) 1993-01-25 1997-09-23 Aust & Taylor Medical Corporation Surgical instrument
EP0608853B1 (en) 1993-01-26 2003-04-02 Terumo Kabushiki Kaisha Vascular dilatation instrument and catheter
JP3345147B2 (en) 1993-01-26 2002-11-18 テルモ株式会社 Vasodilators and catheters
ATE199834T1 (en) 1993-01-28 2001-04-15 Angiomed Ag ONE-PIECE GUIDE PART AND METHOD FOR MAKING THE SAME
US5358493A (en) 1993-02-18 1994-10-25 Scimed Life Systems, Inc. Vascular access catheter and methods for manufacture thereof
US5336205A (en) 1993-02-25 1994-08-09 Target Therapeutics, Inc. Flow directed catheter
US5365943A (en) 1993-03-12 1994-11-22 C. R. Bard, Inc. Anatomically matched steerable PTCA guidewire
US5769796A (en) * 1993-05-11 1998-06-23 Target Therapeutics, Inc. Super-elastic composite guidewire
US5772609A (en) 1993-05-11 1998-06-30 Target Therapeutics, Inc. Guidewire with variable flexibility due to polymeric coatings
US5409015A (en) * 1993-05-11 1995-04-25 Target Therapeutics, Inc. Deformable tip super elastic guidewire
ES2089775T3 (en) * 1993-05-19 1996-10-01 Schneider Europ Ag GUIDE WIRE.
JP3383009B2 (en) 1993-06-29 2003-03-04 テルモ株式会社 Vascular catheter
US5562619A (en) 1993-08-19 1996-10-08 Boston Scientific Corporation Deflectable catheter
NL9301642A (en) 1993-09-22 1995-04-18 Cordis Europ Microcatheter.
US5601539A (en) 1993-11-03 1997-02-11 Cordis Corporation Microbore catheter having kink-resistant metallic tubing
US5720300A (en) 1993-11-10 1998-02-24 C. R. Bard, Inc. High performance wires for use in medical devices and alloys therefor
DE69432359T2 (en) 1993-11-12 2003-12-24 Micro Interventional Systems P CATHETER WITH SMALL DIAMETER AND HIGH TORQUE
US5507301A (en) * 1993-11-19 1996-04-16 Advanced Cardiovascular Systems, Inc. Catheter and guidewire system with flexible distal portions
US5807075A (en) 1993-11-23 1998-09-15 Sarcos, Inc. Disposable ambulatory microprocessor controlled volumetric pump
US5520194A (en) * 1993-12-07 1996-05-28 Asahi Intecc Co., Ltd. Guide wire for medical purpose and manufacturing process of coil thereof
JPH07178176A (en) 1993-12-24 1995-07-18 Terumo Corp Catheter
US5488959A (en) * 1993-12-27 1996-02-06 Cordis Corporation Medical guidewire and welding process
US5571073A (en) 1994-01-28 1996-11-05 Cordis Corporation Catheter flexible tip assembly
US5569218A (en) 1994-02-14 1996-10-29 Scimed Life Systems, Inc. Elastic guide catheter transition element
US5911715A (en) 1994-02-14 1999-06-15 Scimed Life Systems, Inc. Guide catheter having selected flexural modulus segments
US5902290A (en) 1994-03-14 1999-05-11 Advanced Cardiovascular Systems, Inc. Catheter providing intraluminal access
US5546958A (en) 1994-03-31 1996-08-20 Lake Region Manufacturing Company, Inc. Guidewire extension system with tactile connection indication
US5406960A (en) 1994-04-13 1995-04-18 Cordis Corporation Guidewire with integral core and marker bands
US5533985A (en) 1994-04-20 1996-07-09 Wang; James C. Tubing
US5656011A (en) 1994-04-28 1997-08-12 Epflex Feinwerktechnik Gmbh Endoscope tube system
US6139510A (en) 1994-05-11 2000-10-31 Target Therapeutics Inc. Super elastic alloy guidewire
US5666969A (en) 1994-05-18 1997-09-16 Scimed Life Systems, Inc. Guidewire having multiple radioscopic coils
JP3970341B2 (en) 1994-06-20 2007-09-05 テルモ株式会社 Vascular catheter
US5441055A (en) * 1994-06-27 1995-08-15 Cordis Corporation Guidewire extension wire and connector assembly
US5460187A (en) 1994-07-01 1995-10-24 Boston Scientific Corp. Fluoroscopically viewable guidewire
US5496294A (en) 1994-07-08 1996-03-05 Target Therapeutics, Inc. Catheter with kink-resistant distal tip
US5497785A (en) 1994-07-27 1996-03-12 Cordis Corporation Catheter advancing guidewire and method for making same
US5673707A (en) * 1994-09-23 1997-10-07 Boston Scientific Corporation Enhanced performance guidewire
WO1996009848A1 (en) 1994-09-26 1996-04-04 Medtronic, Inc. Cathether flexible distal tip
US5599305A (en) 1994-10-24 1997-02-04 Cardiovascular Concepts, Inc. Large-diameter introducer sheath having hemostasis valve and removable steering mechanism
US5520645A (en) 1994-10-28 1996-05-28 Intelliwire, Inc. Low profile angioplasty catheter and/or guide wire and method
US5658264A (en) 1994-11-10 1997-08-19 Target Therapeutics, Inc. High performance spiral-wound catheter
ES2181802T3 (en) 1994-11-23 2003-03-01 Micro Interventional Systems I BALLOON CATHETER WITH STRONG TORSION.
US5622184A (en) 1994-11-29 1997-04-22 Applied Medical Resources Corporation Guidewire and method of manufacture
US5599326A (en) 1994-12-20 1997-02-04 Target Therapeutics, Inc. Catheter with multi-layer section
US5569197A (en) 1994-12-21 1996-10-29 Schneider (Usa) Inc Drug delivery guidewire
CA2208554A1 (en) 1994-12-28 1996-07-04 Omrix Biopharmaceuticals S.A. Device for applying one or several fluids
CA2208083A1 (en) 1995-01-04 1996-07-11 Medtronic, Inc. Improved method of soft tip forming
US5797856A (en) 1995-01-05 1998-08-25 Cardiometrics, Inc. Intravascular guide wire and method
US5666968A (en) 1995-03-17 1997-09-16 Intelliwire, Inc. Flexible guide wire with extension capability and guide wire extension for use therewith
US5916178A (en) 1995-03-30 1999-06-29 Medtronic, Inc. Steerable high support guidewire with thin wall nitinol tube
US6325790B1 (en) 1995-04-11 2001-12-04 Cordis Corporation Soft tip catheter
EP0738495B1 (en) * 1995-04-18 2002-06-26 Schneider (Europe) GmbH Pressure measuring guide wire
US5640970A (en) * 1995-04-26 1997-06-24 Cordis Corporation Guidewire having a controlled radiopacity tip
US5551444A (en) 1995-05-31 1996-09-03 Radius Medical Technologies, Inc. Flexible guidewire with radiopaque outer coil and non-radiopaque inner coil
US6273404B1 (en) 1995-06-05 2001-08-14 Scimed Life Systems, Inc. Method of making monolithic hub and strain relief
US5788707A (en) 1995-06-07 1998-08-04 Scimed Life Systems, Inc. Pull back sleeve system with compression resistant inner shaft
US5724989A (en) * 1995-06-20 1998-03-10 The Microspring Company, Inc. Radiopaque medical devices
EP0755693A1 (en) 1995-07-18 1997-01-29 Schneider (Europe) Ag Catheter guide wire
US5746701A (en) 1995-09-14 1998-05-05 Medtronic, Inc. Guidewire with non-tapered tip
US5722424A (en) * 1995-09-29 1998-03-03 Target Therapeutics, Inc. Multi-coating stainless steel guidewire
US6027461A (en) 1995-10-11 2000-02-22 Micro Therapeutics, Inc. Infusion guidewire having fixed core wire and flexible radiopaque marker
US5836892A (en) * 1995-10-30 1998-11-17 Cordis Corporation Guidewire with radiopaque markers
US5843050A (en) 1995-11-13 1998-12-01 Micro Therapeutics, Inc. Microcatheter
US5868685A (en) 1995-11-14 1999-02-09 Devices For Vascular Intervention Articulated guidewire
CA2192045A1 (en) 1995-12-07 1997-06-08 Stephen C. Jacobsen Catheter guide wire apparatus
US5931830A (en) 1995-12-07 1999-08-03 Sarcos L.C. Hollow coil guide wire apparatus for catheters
US6428489B1 (en) 1995-12-07 2002-08-06 Precision Vascular Systems, Inc. Guidewire system
US5833632A (en) 1995-12-07 1998-11-10 Sarcos, Inc. Hollow guide wire apparatus catheters
US20030069522A1 (en) 1995-12-07 2003-04-10 Jacobsen Stephen J. Slotted medical device
US5813996A (en) 1995-12-21 1998-09-29 Scimed Life Systems, Inc. Guide wire extension system with magnetic coupling
US6004279A (en) 1996-01-16 1999-12-21 Boston Scientific Corporation Medical guidewire
US5807249A (en) 1996-02-16 1998-09-15 Medtronic, Inc. Reduced stiffness, bidirectionally deflecting catheter assembly
JP3255271B2 (en) 1996-03-12 2002-02-12 ダイワ精工株式会社 Spinning reel for fishing
US5891056A (en) 1996-03-15 1999-04-06 Advanced Cardiovascular Systems, Inc. Guidewire replacement device with flexible intermediate section
US5682894A (en) 1996-04-26 1997-11-04 Orr; Gregory C. Guide wire
US6488637B1 (en) 1996-04-30 2002-12-03 Target Therapeutics, Inc. Composite endovascular guidewire
US5836926A (en) 1996-05-13 1998-11-17 Schneider (Usa) Inc Intravascular catheter
US6068623A (en) 1997-03-06 2000-05-30 Percusurge, Inc. Hollow medical wires and methods of constructing same
US5916194A (en) 1996-05-24 1999-06-29 Sarcos, Inc. Catheter/guide wire steering apparatus and method
US6017319A (en) 1996-05-24 2000-01-25 Precision Vascular Systems, Inc. Hybrid tubular guide wire for catheters
US6440088B1 (en) 1996-05-24 2002-08-27 Precision Vascular Systems, Inc. Hybrid catheter guide wire apparatus and method
US5690120A (en) 1996-05-24 1997-11-25 Sarcos, Inc. Hybrid catheter guide wire apparatus
US5843244A (en) 1996-06-13 1998-12-01 Nitinol Devices And Components Shape memory alloy treatment
US5827242A (en) 1996-06-21 1998-10-27 Medtronic, Inc. Reinforced catheter body and method for its fabrication
US5676697A (en) 1996-07-29 1997-10-14 Cardiovascular Dynamics, Inc. Two-piece, bifurcated intraluminal graft for repair of aneurysm
US5902254A (en) 1996-07-29 1999-05-11 The Nemours Foundation Cathether guidewire
US6553880B2 (en) 1996-09-16 2003-04-29 Sarcos, Lc Micromachining system
US6014919A (en) 1996-09-16 2000-01-18 Precision Vascular Systems, Inc. Method and apparatus for forming cuts in catheters, guidewires, and the like
US5807279A (en) * 1996-09-27 1998-09-15 Cordis Corporation Guidewire having radiopaque distal tip
US5865768A (en) * 1996-09-30 1999-02-02 Medtronic, Inc. Guide wire
US5971975A (en) 1996-10-09 1999-10-26 Target Therapeutics, Inc. Guide catheter with enhanced guidewire tracking
US6001068A (en) 1996-10-22 1999-12-14 Terumo Kabushiki Kaisha Guide wire having tubular connector with helical slits
GB9623402D0 (en) 1996-11-08 1997-01-08 Smiths Industries Plc Catheter assemblies and inner cannulae
US5904657A (en) 1997-02-26 1999-05-18 Unsworth; John D. System for guiding devices in body lumens
US5924998A (en) * 1997-03-06 1999-07-20 Scimed Life System, Inc. Guide wire with hydrophilically coated tip
US6251086B1 (en) * 1999-07-27 2001-06-26 Scimed Life Systems, Inc. Guide wire with hydrophilically coated tip
US5800454A (en) 1997-03-17 1998-09-01 Sarcos, Inc. Catheter deliverable coiled wire thromboginic apparatus and method
US5911717A (en) 1997-03-17 1999-06-15 Precision Vascular Systems, Inc. Catheter deliverable thrombogenic apparatus and method
US5906618A (en) 1997-03-20 1999-05-25 Vanderbilt University Microcatheter with auxiliary parachute guide structure
EP0988081A1 (en) 1997-06-04 2000-03-29 Advanced Cardiovascular Systems, Inc. Steerable guidewire with enhanced distal support
US5951539A (en) 1997-06-10 1999-09-14 Target Therpeutics, Inc. Optimized high performance multiple coil spiral-wound vascular catheter
US6183420B1 (en) * 1997-06-20 2001-02-06 Medtronic Ave, Inc. Variable stiffness angioplasty guide wire
US5947940A (en) 1997-06-23 1999-09-07 Beisel; Robert F. Catheter reinforced to prevent luminal collapse and tensile failure thereof
US5980471A (en) 1997-10-10 1999-11-09 Advanced Cardiovascular System, Inc. Guidewire with tubular connector
US6132388A (en) * 1997-10-16 2000-10-17 Scimed Life Systems, Inc. Guide wire tip
US6056702A (en) * 1998-10-02 2000-05-02 Cordis Corporation Guidewire with outer sheath
US5935108A (en) 1997-11-14 1999-08-10 Reflow, Inc. Recanalization apparatus and devices for use therein and method
US6106485A (en) 1997-11-18 2000-08-22 Advanced Cardivascular Systems, Inc. Guidewire with shaped intermediate portion
US6273876B1 (en) 1997-12-05 2001-08-14 Intratherapeutics, Inc. Catheter segments having circumferential supports with axial projection
US6251092B1 (en) 1997-12-30 2001-06-26 Medtronic, Inc. Deflectable guiding catheter
US6063200A (en) 1998-02-10 2000-05-16 Sarcos L.C. Three-dimensional micro fabrication device for filamentary substrates
US6346091B1 (en) 1998-02-13 2002-02-12 Stephen C. Jacobsen Detachable coil for aneurysm therapy
US6022369A (en) 1998-02-13 2000-02-08 Precision Vascular Systems, Inc. Wire device with detachable end
KR19990072499A (en) 1998-02-19 1999-09-27 리페르트 존 Catheter guidewire apparatus with location specific flexibility
JPH11299899A (en) * 1998-04-16 1999-11-02 Excel Medi Kk Guide wire for catheter
US6494907B1 (en) * 1998-04-28 2002-12-17 Intratherapeutics, Inc. Braided stent
US6171296B1 (en) 1998-04-28 2001-01-09 Microtherapeutics, Inc. Flow directed catheter
US6306105B1 (en) * 1998-05-14 2001-10-23 Scimed Life Systems, Inc. High performance coil wire
US6368316B1 (en) 1998-06-11 2002-04-09 Target Therapeutics, Inc. Catheter with composite stiffener
US6045547A (en) 1998-06-15 2000-04-04 Scimed Life Systems, Inc. Semi-continuous co-extruded catheter shaft
US6048339A (en) 1998-06-29 2000-04-11 Endius Incorporated Flexible surgical instruments with suction
US6547779B2 (en) 1998-07-22 2003-04-15 Endovasix, Inc. Flexible flow apparatus and method for the disruption of occlusions
US6106488A (en) 1998-08-11 2000-08-22 Scimed Life Systems, Inc. Flexural rigidity profile guidewire tip
US6022343A (en) 1998-09-03 2000-02-08 Intratherapeutics, Inc. Bridged coil catheter support structure
US6059769A (en) 1998-10-02 2000-05-09 Medtronic, Inc. Medical catheter with grooved soft distal segment
DE19982467T1 (en) * 1998-11-06 2001-02-22 Furukawa Electric Co Ltd Medical guidewire based on NiTi and method of manufacturing the same
US6214042B1 (en) 1998-11-10 2001-04-10 Precision Vascular Systems, Inc. Micro-machined stent for vessels, body ducts and the like
US6063101A (en) 1998-11-20 2000-05-16 Precision Vascular Systems, Inc. Stent apparatus and method
JP2002058748A (en) * 1998-12-11 2002-02-26 Paiorakkusu:Kk Guide wire for catheter and production method thereof
US6228073B1 (en) 1998-12-15 2001-05-08 Medtronic, Inc. Angiography luer hub having wings proximal to the plurality of grips and strain relief
US6142958A (en) * 1998-12-23 2000-11-07 Radi Medical Systems Ab Sensor and guide wire assembly
US6464650B2 (en) 1998-12-31 2002-10-15 Advanced Cardiovascular Systems, Inc. Guidewire with smoothly tapered segment
US6398758B1 (en) 1999-02-16 2002-06-04 Stephen C. Jacobsen Medicament delivery system
US6500147B2 (en) * 1999-02-22 2002-12-31 Medtronic Percusurge, Inc. Flexible catheter
US6887235B2 (en) 1999-03-24 2005-05-03 Micrus Corporation Variable stiffness heating catheter
DK1040843T3 (en) * 1999-03-29 2006-01-30 William Cook Europe As A guidewire
US6302870B1 (en) 1999-04-29 2001-10-16 Precision Vascular Systems, Inc. Apparatus for injecting fluids into the walls of blood vessels, body cavities, and the like
EP1092449A1 (en) 1999-04-30 2001-04-18 Usaminanotechnology, Inc. Catheter and guide wire
US6183410B1 (en) 1999-05-06 2001-02-06 Precision Vascular Systems, Inc. Radiation exposure device for blood vessels, body cavities and the like
US6758830B1 (en) 1999-05-11 2004-07-06 Atrionix, Inc. Catheter positioning system
US6478778B1 (en) 1999-05-28 2002-11-12 Precision Vascular Systems, Inc. Apparatus for delivering fluids to blood vessels, body cavities, and the like
US6355027B1 (en) 1999-06-09 2002-03-12 Possis Medical, Inc. Flexible microcatheter
US6368315B1 (en) 1999-06-23 2002-04-09 Durect Corporation Composite drug delivery catheter
US6193686B1 (en) 1999-06-30 2001-02-27 Advanced Cardiovascular Systems, Inc. Catheter with enhanced flexibility
US6203485B1 (en) 1999-10-07 2001-03-20 Scimed Life Systems, Inc. Low attenuation guide wire for intravascular radiation delivery
US6352515B1 (en) * 1999-12-13 2002-03-05 Advanced Cardiovascular Systems, Inc. NiTi alloyed guidewires
US6451026B1 (en) * 1999-12-21 2002-09-17 Advanced Cardiovascular Systems, Inc. Dock exchange system for composite guidewires
US6579246B2 (en) 1999-12-22 2003-06-17 Sarcos, Lc Coronary guidewire system
US6290656B1 (en) 1999-12-30 2001-09-18 Advanced Cardiovascular Systems, Inc. Guide wire with damped force vibration mechanism
US6602280B2 (en) 2000-02-02 2003-08-05 Trivascular, Inc. Delivery system and method for expandable intracorporeal device
US6491671B1 (en) 2000-03-14 2002-12-10 Vanderbilt University Microcatheter with hemodynamic guide structure
CA2409111C (en) 2000-05-17 2005-12-27 Cook Vascular Incorporated Lead removal apparatus
US6530934B1 (en) 2000-06-06 2003-03-11 Sarcos Lc Embolic device composed of a linear sequence of miniature beads
JP2002095755A (en) * 2000-07-06 2002-04-02 Japan Lifeline Co Ltd Medical guide wire
US6602207B1 (en) * 2000-07-19 2003-08-05 Scimed Life Systems, Inc. Guide wire stiffness transition element
US6428512B1 (en) 2000-10-10 2002-08-06 Advanced Cardiovascular Systems, Inc. Guidewire with improved lesion measurement
US6500130B2 (en) * 2000-12-21 2002-12-31 Scimed Life Systems, Inc. Steerable guidewire
US6524301B1 (en) 2000-12-21 2003-02-25 Advanced Cardiovascular Systems, Inc. Guidewire with an intermediate variable stiffness section
JP4061840B2 (en) 2000-12-28 2008-03-19 凸版印刷株式会社 Hole transporting compound and organic thin film light emitting device for organic thin film light emitting device
US6506205B2 (en) * 2001-02-20 2003-01-14 Mark Goldberg Blood clot filtering system
US6623448B2 (en) 2001-03-30 2003-09-23 Advanced Cardiovascular Systems, Inc. Steerable drug delivery device
US6636758B2 (en) 2001-05-01 2003-10-21 Concentric Medical, Inc. Marker wire and process for using it
ATE347393T1 (en) 2001-07-05 2006-12-15 Precision Vascular Systems Inc MEDICAL DEVICE HAVING A TORQUE-TRANSMITTING SOFT END PIECE AND METHOD FOR SHAPING IT
JP4099963B2 (en) 2001-09-03 2008-06-11 コニカミノルタホールディングス株式会社 Image forming apparatus
US6918882B2 (en) * 2001-10-05 2005-07-19 Scimed Life Systems, Inc. Guidewire with stiffness blending connection
JP2003334253A (en) * 2002-05-20 2003-11-25 Nipro Corp Guide wire
US6652508B2 (en) 2001-11-09 2003-11-25 Scimed Life Systems, Inc. Intravascular microcatheter having hypotube proximal shaft with transition
JP3762290B2 (en) * 2001-12-03 2006-04-05 朝日インテック株式会社 Medical guidewire
US6682493B2 (en) 2001-12-03 2004-01-27 Scimed Life Systems, Inc. High torque guidewire
US6830638B2 (en) * 2002-05-24 2004-12-14 Advanced Cardiovascular Systems, Inc. Medical devices configured from deep drawn nickel-titanium alloys and nickel-titanium clad alloys and method of making the same
US6730095B2 (en) 2002-06-26 2004-05-04 Scimed Life Systems, Inc. Retrograde plunger delivery system
US6866642B2 (en) 2002-11-25 2005-03-15 Advanced Cardiovascular Systems, Inc. Enhanced method for joining two core wires
US20040167437A1 (en) 2003-02-26 2004-08-26 Sharrow James S. Articulating intracorporal medical device
JP4236965B2 (en) 2003-03-19 2009-03-11 三菱エンジニアリングプラスチックス株式会社 Polyamide resin granules
CN1230914C (en) 2003-03-25 2005-12-07 浙江大学 Schottky diode prototyping element and preparation thereof
JP4213069B2 (en) 2003-09-02 2009-01-21 五洋建設株式会社 Marine seed plant growing material, production method of marine seed plant growing material, and creation method of marine seed plant growing ground
JP4213070B2 (en) 2004-03-30 2009-01-21 川崎重工業株式会社 Railway soundproofing equipment
US7854467B2 (en) * 2004-11-05 2010-12-21 General Motors Corporation Airflow control devices based on active materials
US8205631B2 (en) * 2008-11-19 2012-06-26 Autoliv Asp, Inc. Active material actuated vent valve

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