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WO2004093957A1 - Medical device - Google Patents

Medical device

Info

Publication number
WO2004093957A1
WO2004093957A1 PCT/US2003/037821 US0337821W WO2004093957A1 WO 2004093957 A1 WO2004093957 A1 WO 2004093957A1 US 0337821 W US0337821 W US 0337821W WO 2004093957 A1 WO2004093957 A1 WO 2004093957A1
Authority
WO
Grant status
Application
Patent type
Prior art keywords
member
reinforcing
inner
tubular
embodiments
Prior art date
Application number
PCT/US2003/037821
Other languages
French (fr)
Inventor
Stephen Griffin
Elaine Lim
Gregory E. Mirigian
Original Assignee
Boston Scientific Limited
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date

Links

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
    • A61M25/0043Catheters; Hollow probes characterised by structural features
    • A61M25/0054Catheters; Hollow probes characterised by structural features with regions for increasing flexibility
    • 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
    • A61M25/0009Making of catheters or other medical or surgical tubes
    • A61M25/001Forming the tip of a catheter, e.g. bevelling process, join or taper
    • 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
    • A61M25/0043Catheters; Hollow probes characterised by structural features
    • A61M25/0045Catheters; Hollow probes characterised by structural features multi-layered, e.g. coated
    • 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
    • A61M25/0043Catheters; Hollow probes characterised by structural features
    • A61M25/005Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids
    • A61M25/0051Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids made from fenestrated or weakened tubing layer
    • 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
    • A61M25/0043Catheters; Hollow probes characterised by structural features
    • A61M25/005Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids
    • A61M25/0053Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids having a variable stiffness along the longitudinal axis, e.g. by varying the pitch of the coil or braid
    • 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
    • A61M25/0067Catheters; Hollow probes characterised by the distal end, e.g. tips
    • A61M25/0068Static characteristics of the catheter tip, e.g. shape, atraumatic tip, curved tip or tip structure
    • 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
    • A61M25/0097Catheters; Hollow probes characterised by the hub
    • 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
    • A61M25/0105Steering means as part of the catheter or advancing means; Markers for positioning
    • A61M25/0108Steering means as part of the catheter or advancing means; Markers for positioning using radio-opaque or ultrasound markers
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION, OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS, OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS, OR SURGICAL ARTICLES
    • A61L29/00Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/02Inorganic materials
    • 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
    • A61M25/0043Catheters; Hollow probes characterised by structural features
    • A61M25/0045Catheters; Hollow probes characterised by structural features multi-layered, e.g. coated
    • A61M2025/0046Coatings for improving slidability
    • 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
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/02General characteristics of the apparatus characterised by a particular materials
    • A61M2205/0216Materials providing elastic properties, e.g. for facilitating deformation and avoid breaking
    • 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
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/02General characteristics of the apparatus characterised by a particular materials
    • A61M2205/0227Materials having sensing or indicating function, e.g. indicating a pressure increase
    • 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
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/02General characteristics of the apparatus characterised by a particular materials
    • A61M2205/0266Shape memory materials

Abstract

A medical device includes a shaft having an elongated inner tubular member and an elongated tubular reinforcing member disposed over a portion of the inner tubular member. In some embodiments, the reinforcing member is disposed about a proximal portion of the inner tubular member such that a distal portion of the inner tubular member is free from the reinforcing member. In some embodiments, the at least a portion of an outer surface of the inner tubular member is spaced from an inner surface of the reinforcing member. In some embodiments, the shaft can include a tip structure disposed on the distal portion of the inner tubular member. In some such embodiments, reinforcing member has a distal end, and the tip structure is disposed on the distal portion of the inner tubular member adjacent the distal end of the reinforcing member. Additionally, in some embodiments, the reinforcing member can include a plurality of apertures defined therein, for example, to enhance the flexibility or other such characteristics of all of portions of the reinforcing member.

Description

MEDICAL DEVICE

Field of the Invention The invention relates generally to medical devices. More specifically, the invention relates to a medical device, such as a catheter or the like, including an elongated shaft having a reinforcing member disposed about a portion of the shaft.

Background A wide variety of medical devices have been developed for intracorporal use. Elongated medical devices are commonly used in to facilitate navigation through and/or treatment within the anatomy of a patient. A variety of elongate medical devices such as catheters, endoscopes and the like have been developed over the past several decades. Because the anatomy of a patient may be very tortuous, it is desirable to combine a number of performance features in such devices. For example, it is sometimes desirable that the device have a relatively high level of pushability and torqueability, particularly near its proximal end. It is also sometimes desirable that a device be relatively flexible, particularly near its distal end. A number of different elongated medical device structures and assemblies are known, each having certain advantages and disadvantages. However, there is an ongoing need to provide alternative elongated medical device structures and assemblies.

Summary of Some Embodiments The invention provides design, material, and manufacturing method alternatives for medical devices. In some embodiments, the medical devices can include a shaft having an elongated inner tubular member and an elongated tubular reinforcing member disposed over a portion of the inner tubular member. In some embodiments, the reinforcing member is disposed about a proximal portion of the inner tubular member such that a distal portion of the inner tubular member is free of the reinforcing member. In some embodiments, the at least a portion of an outer surface of the inner tubular member is spaced from an inner surface of the reinforcing member. In some embodiments, the shaft can include a tip structure disposed on the distal portion of the inner tubular member. In some such embodiments, reinforcing member has a distal end, and the tip structure is disposed on the distal portion of the inner tubular member adjacent the distal end of the reinforcing member. Additionally, in some embodiments, the reinforcing member can include a plurality of apertures defined therein, for example, to enhance the flexibility or other such characteristics of all of portions of the reinforcing member.

The above summary of some embodiments is not intended to describe each 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 Drawings The invention may be more completely understood in consideration of the following detailed description of various embodiments of the invention in connection with the accompanying drawings, in which:

Figure 1 is a partial side plan view of a medical device in accordance with one example embodiment of the invention, shown as a guide or diagnostic catheter; Figure 2 a partial cross sectional view of a portion of the medical device of

Figure 1;

Figure 3 is a partial cross sectional view of a portion of the medical device of Figure 1, taken along line 3-3 of Figure 1;

Figure 4 is a partial cross sectional view similar to the view of Figure 3, but of another example embodiment of a medical device;

Figure 5 is a partial cross sectional view similar to the view of Figure 3, but of another example embodiment of a medical device;

Figure 6 is a partial cross sectional view similar to the view of Figure 3, but of another example embodiment of a medical device; and Figure 7 is a cross sectional view taken along line 7-7 of Figure 1.

While the invention is amenable to various modifications and alternative forms, specifics thereof have been shown by way of example in the drawings and will be described in detail. It should be understood, however, that the intention is not to limit the invention to the particular embodiments described. On the contrary, the intention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention. Detailed Description of Some Embodiments of the Invention 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 include numbers that are rounded to the nearest significant figure.

Weight percent, percent by weight, wt%, wt-%, % by weight, and the like are synonyms that refer to the concentration of a substance as the weight of that substance divided by the weight of the composition and multiplied by 100.

The recitation of numerical 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 term "or" is generally employed in its sense including "and/or" unless the content clearly dictates otherwise.

The following detailed description should be read with reference to the drawings in which similar elements in different drawings are numbered the same. The drawings, which are not necessarily to scale, depict illustrative embodiments and are not intended to limit the scope of the invention.

Refer now to Figure 1 which illustrates a medical device 10 in accordance with one example embodiment. In the embodiment shown, the medical device 10 is in the form of a guide or diagnostic catheter. Although set forth with specific reference to a guide or diagnostic catheter in the example embodiments shown in the Figures and discussed below, the invention may relate to virtually any medical device including an elongate shaft or member having a reinforcing member disposed thereon. For example, the invention may be applied to medical devices such as a balloon catheter, an atherectomy catheter, a drug delivery catheter, a stent delivery catheter, an endoscope, an introducer sheath (if the sheath includes a reinforcing member), a fluid delivery device, other infusion or aspiration devices, device delivery (i.e. implantation) devices, and the like. Thus, while the Figures and descriptions below are directed toward a guide or diagnostic catheter, in other applications sizes in terms of diameter and length may vary widely, depending upon the desired properties of a particular device. For example, in some devices, lengths may range from about 1-300 centimeters or more, while outside diameters may range from about IF to about 20F, or even more in some embodiments.

As shown in Figure 1, the catheter 10 can include an elongate shaft 12 including a proximal portion 16 having a proximal end 18, and distal portion 20 having a distal end 22. The shaft 12 is a generally tubular member defining a lumen 15 therein. A manifold 14 can be connected to the proximal end of the elongate shaft 12, and include a lumen and/or other structure to facilitate connection to other medical devices (e.g., syringe, Y-adapter, etc.) and to provide access to 15 lumen within the shaft 12. The manifold may include a hub portion 17 and a strain relief portion 19. In some embodiments, the shaft 12 may include additional devices or structures such as inflation or anchoring members, sensors, optical elements, ablation devices or the like, depending upon the desired function and characteristics of the catheter 10.

The guide or diagnostic catheter 10 may have a length and an outside diameter appropriate for its desired use, for example, to enable intravascular insertion and navigation. For example, the catheter 10 may have a length of about 20cm-250cm and an outside diameter of approximately 1F-10F, when catheter 10 is adapted as a guide catheter. In some embodiments, the catheter 10 can be a microcatheter that is adapted and/or configured for use within small anatomies of the patient. For example, some embodiments are particularly useful in treating targets located in tortuous and narrow vessels, for example in the neurovascular system, or in certain sites within the coronary vascular system, or in sites within the peripheral vascular system such as superficial femoral, popliteal, or renal arteries. The target site in some embodiments is a neurovascular site, such as site in the brain, which is accessible only via a tortuous vascular path, for example, a vascular path containing a plurality of bends or turns which may be greater than 90° turns, and/or involving vessels which are in the range of about 8mm or less, and in some cases as small as 2-3 mm or less, in diameter. However, it is contemplated that the catheter may be used in other target sites within the anatomy of a patient. In some embodiments, the catheter can include an outside diameter in the range of approximately 1F-4F.

While in some embodiments, the catheter 10 can be described in terms of intravascular use, in other embodiments the guide or diagnostic catheter 10 may be suited for other uses in the digestive system, soft tissues, or any other use including insertion into an organism for medical uses. For example, in some embodiments, the catheter 10 may be significantly shorter and used as an introducer sheath, for example, while in other embodiments the catheter 10 may be adapted for other medical procedures. The guide or diagnostic catheter 10 may also include additional structure and materials that are substantially conventional.

Additionally, although depicted as including a generally round cross-sectional shape, it can be appreciated that the shaft 12 can include other cross-sectional shapes or combinations of shapes without departing from the spirit of the invention. For example, the cross-sectional shape of the generally tubular shaft 12 may be oval, rectangular, square, triangular, polygonal, and the like, or any other suitable shape, depending upon the desired characteristics.

Refer now to Figure 2, which shows a partial cross sectional view the shaft 12 including the proximal portion 16, the distal portion 20, and the manifold 14 connected to the proximal end 18. The shaft 12 can include an inner tubular member 24 defining the lumen 15. The shaft 12 can also include a reinforcing member 26 disposed about a portion of the inner tubular member 24, and a. distal tip structure 28 disposed about a distal portion of the inner tubular member 24. Some example structures and components for use in each of these structures will now be discussed in greater detail. The inner tubular member 24 can extend from a point within the distal portion

20 to a point within the proximal portion 16 of the shaft 12. The length of the inner tubular member 24 can vary, depending upon, for example, the length of the shaft 12, the desired characteristics and functions of the catheter 10, and other such parameters. In some embodiments, the inner tubular member 24 can extend substantially the entire length of the shaft 12, for example, from a point adjacent the proximal end 18 to a point adjacent the distal end 22. For example, the length of the inner tubular member 24 can be in the range of about 1-300 centimeters or more, or in some embodiments in the range of about 20cm-250cm. In some embodiments, the inner tubular member 24 can include a proximal portion 33 and a distal portion 35, which can be any proximal or distal sections of the inner tubular member 24, but in some cases can be defined with regard to the placement of the reinforcing member 26 along the length of the inner tubular member. For example, in some embodiments, the distal portion 35 can be any portion of the inner tubular member 24 that is distal of the reinforcing member 26, while the proximal portion 35 can be any portion of the inner tubular member 24 that is disposed within, or is proximal of a distal end 39 reinforcing member 26. In some embodiments, the distal portion 35 can have a length in the range of 1 cm or greater, or in the range of about 2 cm or greater, and in some embodiments in the range of about 3 to about 20 cm. As indicated above, the inner tubular member 24 defines a lumen 15. The lumen 15 can be adapted and/or configured to facilitate, for example, insertion of other medical devices (e.g., guide wires, balloon catheters, etc.) there through, and/or to facilitate injection of fluids (e.g., radiopaque dye, saline, drugs, inflation fluid, etc.) there through. The size of the lumen can vary, depending upon the desired characteristics and intended use. In some embodiments, the inner tubular member 24 can have an inner diameter, defining the lumen 15, that is in the range of about 0.01 to about 0.05 inch in size, and in some embodiments, in the range of about 0.015 to about 0.03 inch in size, and in some embodiments, in the range of about 0.016 to about 0.026 inch in size. Additionally, in some embodiments, the inner tubular member 24 can have an outer diameter that is in the range of about 0.011 to about 0.055 inch in size, and in some embodiments, in the range of about 0.015 to about 0.03 inch in size, and in some embodiments, in the range of about 0.019 to about 0.029 inch in size. It should be understood however, that these dimensions are provided by way of example embodiments only, and that in other embodiments, the size of the inner and outer diameter of the inner tubular member 24 can vary greatly from the dimensions given, depending upon the desired characteristics and function of the device. In some embodiments, the inner tubular member 24, other portions of the shaft 12, can define one or more additional lumens depending upon the desired characteristics and function of the catheter 10, and such additional lumens can be shaped, size, adapted and/or configured the same as or different from lumen 15, depending upon the desired characteristic and functions.

The inner tubular member 24 may be one or more layers. As best seen in Figure 3, the inner tubular member 24 may be multi-layered. In the illustrative embodiment, the inner tubular member 24 may include an outer layer 30, and an inner layer 34. It should be understood that more or fewer layers can be used depending upon the desired characteristics of the device. Furthermore, while an outer layer 30 and inner layer 34 are described with respect to the particular embodiment, these layers 30, 34 may be provided as a single layer. For example, the inner layer 34 and outer layer 30 may be provided separately, but attached or combined together to physically form a single layer.

Inner layer 34 and outer layer 30 may be made of any suitable material and by any suitable process, the materials and processes varying with the particular application. Examples of some suitable materials include, but are not limited to, polymers, metals, metal alloys, or composites or combinations thereof. Some examples of some suitable polymers can include, but are not limited to, polyoxymethylene (POM), polybutylene terephthalate (PBT), polyether block ester, polyether block amide (PEBA), fluorinated ethylene propylene (FEP), polyethylene (PE), polypropylene (PP), polyvinylchloride (PVC), polyurethane, polytetrafluoroethylene (PTFE), polyether-ether ketone (PEEK), polyimide, polyamide, polyphenylene sulfide (PPS), polyphenylene oxide (PPO), polysufone, nylon, perfluoro(propyl vinyl ether) (PFA), polyether-ester, polymer/metal composites, etc., or mixtures, blends or combinations thereof, and may also include or be made up of a lubricous polymer. One example of a suitable polyether block ester is available under the trade name ARNITEL, and one suitable example of a polyether block amide (PEBA) is available under the trade name PEBAX®, from ATOMCHEM POLYMERS, Birdsboro, Pa.

The inner layer 34 may include a lubricious polymer such as HDPE or PTFE, for example, or a copolymer of tetrafluoroethylene with perfluoroalkyl vinyl ether (PFA) (more specifically, perfluoropropyl vinyl ether or perfluoromethyl vinyl ether), or the like. The outer layer 30 may include a flexible polymer such as polyether block amide or polyether-ester elastomer. Additionally, in some embodiments, the polymer material of the inner layer 34 and/or outer layer 30 can be blended with a liquid crystal polymer (LCP). For example, in some embodiments, the mixture can contain up to about 5% LCP. This has been found in some embodiments to enhance torqueability.

Additionally, as suggested above, in some embodiments, the inner tubular member 24 may include or be made of metal or metal alloys. Some examples of suitable metals and metal alloys can include stainless steel, such as 304V, 304L, and 316L stainless steel; nickel-titanium alloy such as a superelastic (i.e. pseudoelastic) or linear elastic nitinol; nickel-chromium alloy; nickel-chromium-iron alloy; cobalt alloy; tungsten or tungsten alloys; tantalum or tantalum alloys, gold or gold 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); or the like; or other suitable metals, or combinations or alloys thereof. In some embodiments, it is desirable to use metals, or metal alloys that are suitable for metal joining techniques such as welding, soldering, brazing, crimping, friction fitting, adhesive bonding, etc.

The inner tubular member 24 can be formed by any suitable method or technique. For example in some embodiments, the inner layer 34 can be formed separately, and thereafter the outer layer 30 can be disposed thereon by suitable techniques, such as extrusion, co-extrusion, interrupted layer co-extrusion (ILC), coating, heat shrink techniques, casting, molding, or by fusing one or several segments of an outer layer material end-to-end about the inner layer 34, or the like. In some other embodiments, the layers 30/34 may be formed together using suitable techniques, such as extrusion, co-extrusion, interrupted layer co-extrusion (ILC), heat shrink techniques, fusing, or the like. In yet other embodiments, the layers 30/34 can be formed separately, such as by extrusion, co-extrusion, interrupted layer co- extrusion (ILC), casting, molding, heat shrink techniques, fusing, or the like, and thereafter coupled or connected together using suitable techniques, such as heat shrink techniques, friction fitting, mechanically fitting, chemically bonding, thermally bonding, welding (e.g., resistance, Rf, or laser welding), soldering, brazing, adhesive bonding, crimping, or the use of a connector member or material, or the like, or combinations thereof.

The inner tubular member 24 may have a uniform stiffness, or may vary in stiffness along its length. For example, a gradual reduction in stiffness from the proximal end to the distal end thereof may be achieved, depending upon the desired characteristics. The gradual reduction in stiffness may be continuous or may be stepped, and may be achieved, for example, by varying the structure, such as the size or thickness of one or more of the layers 30/34, or for example, by varying the materials used in one or more of the layers 30/34. Such variability in characteristics and materials can be achieved, for example, by using techniques such as ILC, or by fusing together separate extruded tubular segments. Additionally, the inner and/or the outer layer, 34/30 or both, may be impregnated with, or be made of or include a radiopaque material to facilitate radiographic visualization. Radiopaque materials are understood to be materials capable of producing a relatively bright image on a fluoroscopy screen or another imaging technique during a medical procedure. This relatively bright image aids the user of catheter 10 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 radiopaque filler, and the like. Likewise, in some embodiments, the inner and/or the outer layer, 34/30 or both, may be impregnated with, or be made of or include a material that may aid in MRI imaging. Some materials that exhibit these characteristics include, for example, tungsten, Elgiloy, MP35N, nitinol, and the like, and others. Those skilled in the art will recognize that these materials can vary widely without departing from the spirit of the invention. Additionally, although depicted as including a generally round cross-sectional shape, it can be appreciated that the inner tubular member 24 can include other cross- sectional shapes or combinations of shapes without departing from the spirit of the invention. For example, the cross-sectional shape of the inner tubular member 24 may be oval, rectangular, square, triangular, polygonal, and the like, or any other suitable shape, depending upon the desired characteristics.

Referring to Figures 2 and 3, the reinforcing member 26 can also be a generally tubular member including a proximal region 36 having a proximal end 37 and a distal region 38 having a distal end 39. The reinforcing member 26 can be disposed about at least a portion of the inner tubular member 24 at a location along the length of the shaft 12 between proximal end 18 and distal end 22. In the embodiment shown, the reinforcing member 26 is disposed about the inner tubular member 26 along the proximal portion 16 of the shaft 12, but it should be understood that other locations are possible. The length of the reinforcing member 26 can also vary, depending upon, for example, the length of the shaft 12, the desired characteristics and functions of the catheter 10, and other such parameters. In some embodiments, the reinforcing member 26 has a length that allows it to be disposed over the majority of the length of the inner tubular member 24, and in some embodiments, is disposed about all but up to the distal most 15 cm or less of the inner tubular member 24. For example, the length of the inner tubular member 24 can be in the range of about 1-299 centimeters or more, or in some embodiments in the range of about 19cm-249 cm.

Referring to Figure 3, the reinforcing member 26 defines a lumen 40 that can be adapted and/or configured to house or surround a portion of the inner tubular member 24. In some embodiments, the reinforcing member 26 can have an inner diameter, defining the lumen 40, that is in the range of about 0.015 to about 0.06 inch in size, and in some embodiments, in the range of about 0.02 to about 0.035 inch in size. Additionally, in some embodiments, the reinforcing member 26 can have an outer diameter that is in the range of about 0.016 to about 0.07 in size, and in some embodiments, in the range of about 0.02 to about 0.04 inch in size. It should be understood however, that these, and other dimensions provided herein, are by way of example embodiments only, and that in other embodiments, the size of the inner and outer diameter of the reinforcing member 26 can vary greatly from the dimensions given, depending upon the desired characteristics and function of the device. The reinforcing member 26 typically has an inner diameter that is greater than the outer diameter of the inner tubular member 24. As such, the reinforcing member 26 can be disposed about the inner tubular member 24 (i.e. a portion of the inner tubular member 24 is disposed within the lumen 40 of the reinforcing member) such that a space or gap 42 is defined between at least a portion of the outer surface 25 of the inner tubular member 24 and the inner surface 27 of the reinforcing member 26. In some embodiments, the space or gap 42 between at least a portion of the outer surface 25 of the inner tubular member 24 and the inner surface 27 of the reinforcing member 26 is in the range of about 0.0002 to about 0.004 inch in size, and in some embodiments, in the range of about 0.0005 to about 0.003 inch in size. It should be understood however, that these, and other dimensions provided herein, are by way of example embodiments only, and that in other embodiments, the size of the space or gap 42 can vary greatly from the dimensions given, depending upon the desired characteristics and function of the device.

Typically, the gap or space 42 remains open or unfilled by any other structure of the catheter along substantially the entire length of the reinforcing member 26, with the exception of small coupling points adjacent the proximal and distal ends 37/39 of the reinforcing member, for example, as will be set forth in more detail below. For example, in some embodiments, the gap or space 42 can extend between the outer surface 25 of the inner tubular member 24 and the inner surface 27 of the reinforcing member 26 along the length of the reinforcing member 26 in the range of about 50% or greater, 75% or greater, 90% or greater, or 95% or greater of the entire length of the reinforcing member 26. However, in other embodiments, other attachment points along the length of the reinforcing member 26 may be used, and as a result, multiple gaps or spaces may be created that may be separated by these additional attachment points, which may, in effect, fill portions of the gap 42. Still, such multiple gaps or spaces may still collectively extend along a substantial portion of the length of the reinforcing member, for example, in percentages of the total length as given above. As such, the reinforcing member 26 can act to reinforce or impart desired properties, such as tortional and lateral rigidity, to the catheter shaft 12, but allow at least the portion of the inner tubular member 24 surrounded by the gap or space 42 to move laterally within the lumen 40. Some examples of structure, methods, and techniques of coupling the reinforcing member 26 to the inner tubular member 24 will be discussed in more detail below. The reinforcing member 26 can be adapted and/or configured to have a desired level of stiffness, torqueability, flexibility, and/or other characteristics. Those of skill in the art and others will recognize that the dimensions, structure, and materials of the reinforcing member 26 are dictated primary by the desired characteristics, and the function of the final catheter 10, and that any of a broad range of the dimensions, structure, and materials can be used.

The desired stiffness, torquability, lateral flexibility, bendability or other such characteristics of the reinforcing member 26 can be imparted or enhanced by the structure of the reinforcing member 26. For example, the reinforcing member 26 may include a thin wall tubular structure, including one or a plurality of apertures 44, such as grooves, cuts, slits, slots, or the like, formed in a portion of, or along the entire length of, the tubular reinforcing member 26. Such structure may be desirable because it may allow reinforcing member 26, or portions thereof, to have a desired level of laterally flexibility as well as have the ability to transmit torque and pushing forces from the proximal region 36 to the distal region 38. The apertures 44 can be formed in essentially any known way. For example, apertures 44 can be formed by methods such as micro-machining, saw-cutting, laser cutting, grinding, milling, casting, molding, chemically etching or treating, or other known methods, and the like. In some such embodiments, the structure of the reinforcing member 26 is formed by cutting and/or removing portions of the tube to form apertures 44. In some embodiments, the apertures 44 can completely penetrate the reinforcing member 26 such that there is fluid communication between the lumen 40 and the exterior of the reinforcing member 26 through the apertures 44. In some embodiments, the apertures 44 may only partially extend into the structure of the reinforcing member 26, either on the interior or exterior surface thereof. Some other embodiments may include combinations of both complete and partial apertures 44 through the structure of the reinforcing member 26. The shape and size of the apertures 44 can vary, for example, to achieve the desired characteristics. For example, the shape of apertures 44 can vary to include essentially any appropriate shape, such as squared, round, rectangular, pill-shaped, oval, polygonal, elongated, irregular, or the like, and may include rounded or squared edges, and can be variable in length and width, and the like.

Additionally, the spacing, arrangement, and/or orientation of the apertures 44, or in some embodiments, associated spines or beams that may be formed, can be varied to achieve the desired characteristics. For example, the number or density of the apertures 44 along the length of the reinforcing member 26 may vary, depending upon the desired characteristics. For example, the number or proximity of apertures 44 to one another near one end of the reinforcing member 26 may be high, while the number or proximity of slots to one another near the other end of the reinforcing member 26, may be relatively low, or vice versa. For example, in the embodiment shown in Figures 1 and 2, the distal region 38 of the reinforcing member 26 includes a plurality of apertures 44, while the proximal region 36 of the reinforcing member 26 does not include any apertures 44. As such, the distal region 38 can have a greater degree of lateral flexibility relative to the proximal region 36. In some embodiments, the distal about 10 to about 50% of the total length of the reinforcing member 26 can

"include apertures 44 defined therein, while the proximal about 50 to about 90% of the total length of the reinforcing member 26 is free of such a apertures 44. For example, in some embodiments, the distal region 38 having a length in the range of about 30 to about 70 cm includes apertures 44 defined therein, while the remaining length in the proximal region 36 of the reinforcing member is free of such a apertures 44. It should be understood however, that these, and other dimensions provided herein, are by way of example embodiments only, and that in other embodiments, the disposition of apertures 44 can vary greatly from the dimensions given, depending upon the desired characteristics and function of the device. As suggested above, the apertures 44 may be formed such that one or more spines or beams are formed in the tubular reinforcing member 26. Such spines or beams 50 (Figure 1) could include portions of the tubular member 26 that remain after the apertures 44 are formed in the body of the tubular member. Such spines or beams may act to maintain a relatively high degree of tortional stiffness, while maintaining a desired level of lateral flexibility. In some embodiments, some adjacent apertures 44 can be formed such that they include portions that overlap with each other about the circumference of the tube. In other embodiments, some adjacent apertures 44 can be disposed such that they do not necessarily overlap with each other, but are disposed in a pattern that provides the desired degree of lateral flexibility. Additionally, the apertures 44 can be arranged along the length of, or about the circumference of, the reinforcing member 26 to achieve desired properties. For example, the apertures 44 can be arranged in a symmetrical pattern, such as being disposed essentially equally on opposite sides about the circumference of the reinforcing member 26, or equally spaced along the length of the reinforcing member, or can be arranged in an increasing or decreasing density pattern, or can be arranged in a non-symmetric or irregular pattern.

Collectively, these figures and this description illustrate that changes in the arrangement, number, and configuration of slots may vary without departing from the scope of the invention. Some additional examples of arrangements of cuts or slots formed in a tubular body are disclosed in U.S. Patent No. 6,428,489 and in Published U.S. Patent Application No. 09/746,738 (Pub. No. US 2002/0013540), both of which are incorporated herein by reference. Also, some additional examples of arrangements of cuts or slots formed in a tubular body for use in a medical device are disclosed in a U.S. Patent Application entitled "Articulating Intracorporal Medical Device" filed on February 26, 2003 (Atty. Docket No. 1001.1668101), which is also incorporated herein by reference.

In addition to, or as an alternative to the structure of the reinforcing member 26, the materials selected for reinforcing member 26 may be chosen so that it has the desired characteristics. For example, reinforcing member 26 may be formed of materials having a desired modulus of elasticity. The reinforcing member 26 may be formed of any materials suitable for use, dependent upon the desired properties of the catheter 10. Some examples of suitable materials include metals, metal alloys, polymers, or the like, or combinations or mixtures thereof. Some examples of suitable metals and metal alloys include stainless steel, such as 304V, 304L, and 316L 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%'τi, 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, or combinations or alloys thereof. In some embodiments, it is desirable to use metals, or metal alloys that are suitable for metal joining techniques such as welding, soldering, brazing, crimping, friction fitting, adhesive bonding, etc. Additionally, in some embodiments, the reinforcing member 26 may be made of or include, be coated, plated, or clad with a radiopaque or MRI imaging material to facilitate radiographic visualization or MRI imaging.

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 symbol for nickel (Ni), the chemical symbol for titanium (Ti), and an acronym identifying the Naval Ordinance Laboratory (NOL). In some embodiments, nitinol alloys can include in the range of about 50 to about 60 weight percent nickel, with the remainder being essentially titanium. It should be understood, however, that in other embodiment, the range of weight percent nickel and titanium, and or other trace elements may vary from these ranges. Within the family of commercially available nitinol alloys, are categories designated as "superelastic" (i.e. pseudoelastic) and "linear elastic" which, although similar in chemistry, exhibits distinct and useful mechanical properties.

In some embodiments, a superelastic alloy, for example a superelastic nitinol can be used to achieve desired properties. Such alloys typically display a substantial "superelastic plateau" or "flag region" in its stress/strain curve. Such alloys can be desirable in some embodiments because a suitable superelastic alloy will provide a reinforcing member 26 that is exhibits some enhanced ability, relative to some other non-superelastic materials, of substantially recovering its shape without significant plastic deformation, upon the application and release of stress, for example, during placement of the catheter in the body.

In some other embodiments, a linear elastic alloy, for example a linear elastic nitinol can be used to achieve desired properties. For example, in some embodiments, certain linear elastic nitinol alloys can be generated by the application of cold work, directional stress, and heat treatment, such that the material fabricated does not display a substantial "superelastic plateau" or "flag region" in its stress/strain curve. Instead, in such embodiments, as recoverable strain increases, the stress continues to increase in a somewhat 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 DSC and DMTA analysis over a large temperature range. For example, in some embodiments, there is no martensite/austenite phase changes detectable by DSC and DMTA analysis in the range of about -60°C to about 120°C. The mechanical bending properties of such material are therefore generally inert to the effect of temperature over a 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 allows the reinforcing member to exhibit superior "pushability" around tortuous anatomy. One example of a suitable nickel-titanium alloy exhibiting at least some linear elastic properties is FHP-NT alloy commercially available from Furukawa Techno Material Co. of Kanagawa, Japan. Additionally, some examples of suitable nickel-titanium alloy exhibiting at least some linear elastic properties include those disclosed in U.S. Patent Nos. 5,238,004 and 6,508,803, which are incorporated herein by reference.

In some embodiments, the reinforcing member 26 can be formed of a shape- memory material, for example a shape memory alloy such as a shape memory nitinol. In such embodiments, the shape memory effect can be used in the deployment or use of the catheter, for example in causing the reinforcing member 26 to move from a first insertion configuration to a second use configuration, or, for example, for the reinforcing member 26 to "remember" its desired shape after deformation to another shape. For example, in some embodiments, the reinforcing member 26 can include or be made of a shape memory alloy that is martensite at room temperature, and has a final austenite transition temperature (Af) somewhere in the temperature range between room temperature and body temperature. For example, in some such embodiments, the shape memory alloy has a final austenite transition temperature in the range of about 25°C and about 37°C (e.g. body temperature). In some such embodiments, it may be desirable that the final austenite transition temperature be at least slightly below body temperature, to ensure final transition at body temperature. This feature allows the reinforcing member 26 to be inserted into the body of a patient in a martensitic state, and assume its preformed, austenitic shape when exposed to the higher body temperature within the anatomy, or at the target site. In this embodiment, deployment of the reinforcing member 26 can be achieved by a shape memory effect - - as the material warms, it undergoes a transition from martensite to austenite form, causing transformation of the reinforcing member 26 from the first configuration to the second configuration.

In other example embodiments, the reinforcing member 26 can include or be made of a shape -memory alloy that could have a transition temperature Md (wherein M = highest temperature to strain-induced martensite) that is in the range of body temperature (e.g. 37°C) or greater, below which the alloy retains sufficient stress- induced martensitic property to allow placement of the reinforcing member 26 at or above its final austenite transition temperature (Af). In other words, this allows the catheter, including the reinforcing member 26 in its preformed austenitic state, to be inserted and navigated in the anatomy, where the reinforcing member may be exposed to stress that may promote portions thereof to undergo stress-induced martensitic (SIM) transformation. Thereafter, the reinforcing member 26 may recover its preformed, austenitic shape when released from the stress of navigation, at a temperature that may be substantially above the final austenite transition temperature without significant plastic, or otherwise permanent deformation. Additionally, in some such embodiments, the reinforcing member 26 can be constrained, for example, in a delivery device, such as a guide catheter, in a stress-induced martensitic (SIM) state, and recover its preformed, austenitic shape when released from the constraints of the catheter, at a temperature that may be substantially above the final austenite transition temperature without significant plastic, or otherwise permanent deformation. In these embodiment, the final austenite temperature may be quite low, e.g., 4°C or lower, or it may be up to room temperature or higher.

In yet other embodiments, the reinforcing member 26 can include or be made of a shape memory alloy that is martensite at body temperature, and has a final austenite transition temperature (Af) somewhere in the temperature range above body temperature. This feature allows the catheter including the reinforcing member 26 to be navigated in a martensitic state, and maintain a martensitic state until exposed to a temperature higher than body temperature. The reinforcing member 26 can then be heated to the necessary temperature above body temperature to make the transformation from martensite to austenite using an external heating means or mechanism. Such mechanisms may include the injection of heated fluid through the catheter, or other device, the use of electrical or other energy to heat the reinforcing member 26, or other such techniques. In some such embodiments, the shape memory alloy has a final austenite transition temperature in the range of about 37°C to about 45°C. It may be desirable that the final austenite transition temperature be at least slightly above body temperature, to ensure there is not final transition at body temperature. Some examples or Nitinol cylindrical tubes having desired transition temperatures, as noted above, can be prepared according to known methods.

As noted above, the reinforcing member 26 may also be formed of or include polymer materials. Some examples of polymeric materials may include, but are not limited to: poly(L-lactide) (PLLA), ρoly(D,L-lactide) (PLA), polyglycolide (PGA), poly(L-lactide-co-D,L-lactide) (PLLA/PLA), poly(L-lactide-co-glycolide)

(PLLA/PGA), poly(D, L-lactide-co-glycolide) (PLA/PGA), poly(glycolide-co- trimethylene carbonate) (PGA/PTMC), polyethylene oxide (PEO), polydioxanone (PDS), polycaprolactone (PCL), polyhydroxylbutyrate (PHBT), poly(phosphazene), polyD,L-lactide-co-caprolactone) (PLA/PCL), poly(glycolide-co-caprolactone) (PGA/PCL), polyanhydrides (PAN), poly(ortho esters), poly(phoshate ester), poly(amino acid), poly(hydroxy butyrate), polyacrylate, polyacrylamid, poly(hydroxyethyl methacrylate), polyurethane, polysiloxane and their copolymers, or mixtures or combinations thereof. Referring now to Figure 3, the distal portion 20 of the shaft 12 can include a distal region of the inner tubular member 24, and, in some embodiments, additional structure that can be adapted and/or configured to provide a distal tip structure 28 on the distal region of the catheter 10. For example, the distal tip structure 28 can be adapted and/or configured to provide characteristics such as shapability, flexability, steerability, atraumatic characteristics, and the like. For example, distal portion 20 including the inner tubular member 24, can also include one or more additional layers in addition to or disposed on the inner tubular member 24. Such additional layers may be made of any suitable material and by any suitable process, the materials and processes varying with the particular application and characteristics desired. For example, in the embodiment shown in Figure 3, which is a partial cross-sectional view of a portion of the shaft 12, the distal portion 20 can include two additional layers 50 and 52 disposed about the inner tubular member 24. In the embodiment shown, an inner layer 50, which may be a reinforcement layer, such as a coil, braid, or the like, is disposed about the distal region of the inner tubular member 24, and an outer layer 52, such as a sleeve of material, for example, a polymer sleeve or layer, is disposed about the reinforcement layer 50 and the inner tubular member 24. It should be understood that in some embodiments it is not necessary that one or more of the layers include a reinforcing structure such as a coil or braid. It should also be understood that more or fewer layers can be used depending upon the desired characteristics of the device. Additionally, in some embodiments, a reinforcement layer 50 or structure, such as a coil or braid, may be embedded within a layer, or disposed between multiple layers.

Referring to Figure 3, the reinforcement layer 50 illustrated can be a coil that has a generally circular cross-sectional shape, and is appropriately sized for disposal about the distal region of the shaft 12. A broad variety of other shapes and sizes could be used, for example, depending upon the size and shape of the distal region of the shaft. The coil 50 can be formed of a variety of materials including metals, metal alloys, polymers, and the like, for example, those materials discussed above with regard to the reinforcing member 26.

The coil 50 can be formed of round wire or flat ribbon ranging in dimensions to achieve the desired flexibility. In some embodiments, the coil 50 can be a round ribbon in the range of about 0.001-0.015 inches in diameter, and can have a length in the range of about 0.1 to about 20 cm; however, other dimensions and length are contemplated. The coil 50 can be wrapped in a helical fashion by conventional winding techniques. The pitch of adjacent turns of the coil 50 may be tightly wrapped so that each turn touches the succeeding turn or the pitch may be set such that the coil 50 is wrapped in an open fashion. Additionally, in some embodiments, the coil 50 or portions thereof can be made of or include or be coated, plated, or clad with a radiopaque or imaging material, as discussed above. Additionally, other radiopaque or MRI imaging structures can be incorporated into the structure of the distal portion 20, or other parts of the shaft 12. For example, a band, coil, ring, or other such structure made of or including radiopaque or MRI imaging material may be disposed about or within a portion of the shaft, for example, radiopaque or MRI ring 60. Such a structure can be incorporated within or disposed on the shaft using suitable techniques such as adhesive bonding, crimping, friction fitting, mechanically fitting, chemically bonding, thermally bonding, welding (e.g., resistance, Rf, or laser welding), soldering, brazing, or the use of a connector member or material, or the like, or combinations thereof. The outer layer 52 can be a sheath or sleeve of material, such as a polymer material, disposed about the coil 50 and the inner tubular member 24. Some example of suitable polymer materials include those listed above with regard to the inner tubular member, and the like. The outer layer 52 can be constructed and disposed using any appropriate technique, for example, by extrusion, co-extrusion, interrupted layer co-extrusion (ILC), coating, heat shrink techniques, heat bonding, casting, molding, fusing one or several segments of an outer layer material end-to-end, or the like. Securing the outer layer 52 to the coil 50 and/or the inner tubular member 24 may be achieved by the use of the above techniques, or in embodiments where the layer 52 is constructed independently of the other portions of the shaft 12, may be thereafter secured to the coil 50 and/or the inner tubular member 24 using suitable techniques such as adhesive bonding, crimping, friction fitting, mechanically fitting, chemically bonding, thermally bonding, welding (e.g., resistance, Rf, or laser welding), soldering, brazing, or the use of a connector member or material, or the like, or combinations thereof. Additionally, the outer layer 52 may be sized such that at least the portion thereof that is adjacent the reinforcing member has an outer diameter that is about the same as the outer diameter of the reinforcing member 26, so as to maintain a generally constant diameter in the transition between the reinforcing member 26 and the outer layer 52. Additionally, in some embodiments, the outer layer may include a portion that overlaps the distal end of the reinforcing member 26 to provide a smooth transition. In other embodiments, however, a tapered or step down transition may be provided. The distal portion 15 of the elongate shaft 12 may be curved as desired, or be adapted and/or configured to be curved as desired, depending on the particular application. Now some example embodiments of structure, methods, and techniques of coupling structure of the catheter 10, such as the manifold 14, reinforcing member 26, and distal tip structure 28 to the inner tubular member 24, will be discussed in more detail.

Refer now to Figure 3, which illustrates one example embodiment of a portion of a catheter shaft 12, including the inner tubular member 24, the reinforcing member 26, and the distal tip structure 28 as discussed above. The distal region 36 of the reinforcing member 26 can be connected to the inner tubular member 24 using suitable techniques such as adhesive bonding, friction fitting, mechanically fitting, crimping, chemically bonding, thermally bonding, welding (e.g., resistance, Rf, or laser welding), soldering, brazing, or the use of a connector member or material, or the like, or combinations thereof. In the embodiment shown, the distal end 39 of the reinforcing member 26 can be connected to the inner tubular member 24 using an adhesive material 62, for example, a cyanoacrylate, or other suitable type of adhesive. In at least some embodiments, only a relatively small portion of the distal region 38 adjacent the distal end 39 of the reinforcing member 26 is connected to the inner tubular member 24. For example, the adhesive or other material or structure used to make the connection may only extend under or within five or fewer of the apertures 44, or in some embodiments, as shown in Figure 3, three or even two or fewer of the apertures 44. The coil 50 can be slid onto the distal region 38 of the inner tubular member 24, such that it is in line with or butts up to the reinforcing member 26, and can be connected to the inner tubular member 24 using suitable techniques, such as those described above. In some embodiments, the reinforcing member and the coil 50 can be connected to the inner tubular member 24 at the same time and/or using the same attachment material, such as an adhesive. In other embodiments, they may be attached separately and/or using separate attachment techniques. Any radiopaque or MRI structures, such as the ring 60, can be attached to the coil 50, using suitable attachment techniques, as discussed above. For example, the ring 60 may be attached to the coil 50 by crimping the ring to the coil adjacent the distal end 39 of the reinforcing member 26. In such a configuration, the placement of the ring 60 may also aid in providing a more gradual transition or step down in diameter from the reinforcing member 26 to the coil 50. The outer layer 52, such as a polymer material, can be disposed about the ring 60, the coil 50 and the inner tubular member 24. As discussed above, the outer layer 52 may be sized appropriately so as to maintain a generally constant diameter in the transition between the reinforcing member 26 and the outer layer 52, and may include portion 65 that overlaps the distal end of the reinforcing member 26 to provide a smooth transition.

Refer now to Figure 4, which shows an alternative construction similar to that shown in Figure 3, wherein similar elements are numbered the same. In Figure 4, however, a ring 70 of material, such as polymer material, heat shrink material, or the like, is disposed about the inner tubular member 24 under the distal end 39 of the reinforcing member 26. In such embodiments, the use of the ring 70 disposed between the inner tubular member 24 and the reinforcing member 26 can aid in maintaining the bonding and integrity of the joint or connection. Refer now to Figure 5, which shows another alternative construction similar to that shown in Figure 3, wherein similar elements are numbered the same. In Figure 5, however, the ring 60 is absent. Additionally, in this embodiment, the coil 50 extends proximally such that a proximal portion of the coil 50 is disposed about the inner tubular member 24 under the distal end 39 of the reinforcing member 26. In such embodiments, the placement of a proximal portion of the coil 50 between the inner tubular member 24 and the reinforcing member 26 can aid in maintaining the bonding and integrity of the joint or connection. This embodiment also shows a continuous layer of adhesive material 62 that is used to connect the reinforcing member 26 and the coil 50 to the inner tubular member 24. The outer layer 52 can be disposed about the coil 50, the adhesive material 62, and the inner tubular member 24, and may also include a portion 65 that overlaps the distal end of the reinforcing member 26 to provide a smooth transition.

Refer now to Figure 6, which shows another alternative construction similar to that shown in Figure 3, wherein similar elements are numbered the same. In Figure 5, however, the ring 60 is absent. Additionally, this embodiment shows a continuous layer of adhesive material 62 that is used to connect the reinforcing member 26 and the coil 50 to the inner tubular member 24, and also includes an outer layer 52 that includes a cutout or stepped up portion 80 that can accommodate a greater amount of adhesive material. In some embodiments, the adhesive material may also act to connect the outer layer 52 to the shaft 12.

Referring back to Figures 1 and 2, at the proximal end of the shaft 12, the manifold 14 may be secured to the inner tubular member 24 and/or the reinforcing member 26 at the proximal end 18 of the shaft 12 using any suitable technique, for example, by adhesive, friction fitting, mechanically fitting, chemically bonding, thermally bonding, heat shrink materials, molding, casting, welding (e.g., resistance or laser welding), soldering, brazing, the use of an outer sleeve or polymer layer to bond or connect the components, or the like, or combinations thereof. In some embodiments, the distal end of the manifold 14 can be cast, molded or shaped onto the proximal end 16 of the shaft 12 such that is connected to the proximal end 18, and can also act as a connector between the inner tubular member 24 and/or the reinforcing member 26. For example, the manifold may be made of a polymeric material, such as a polycarbonate material, or the like, that could be molded or cast onto the proximal end 16 of the shaft 12. For example, refer now to Figure 7, which shows the manifold 14 attached to the proximal end 16 of the shaft 12. The manifold 14 can be cast, molded or shaped onto the proximal end 16 of the shaft 12 such that it can include a protrusion 91 that extends between and interconnects the inner tubular member 24 and the reinforcing member 26, and may also include an overlapping portion 93 that may help to maintain connection, and may provide a smooth transition between the manifold 14 and the reinforcement member 26.

A lubricious, a hydrophilic, a protective, or other type of coating may be applied over portions or all of the shaft 12. Hydrophobic coatings such as fluoropolymers provide a dry lubricity which improves catheter handling and device exchanges. Lubricious coatings can aid in insertion and steerability. Suitable lubricious polymers are well known in the art and may include silicone and the like, hydrophilic polymers such as polyarylene oxides, polyvinylpyrolidones, 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 (including some polymers) to yield coatings with suitable lubricity, bonding, and solubility. Some other examples of such coatings and materials and methods used to create such coatings can be found in U.S. Patent Nos. 6,139,510 and 5,772,609, which are incorporated herein by reference. It should also be understood that in some embodiments, a degree of MRI compatibility can be imparted into catheter 10. For example, to enhance compatibility with Magnetic Resonance Imaging (MRI) machines, it may be desirable to construct portions of the reinforcing member 26, the coil 50, or other portions of the catheter 10, in a manner, or use materials that would impart, a degree of MRI compatibility. For example, the lengths of relatively conductive structures within the catheter 10 may be limited to lengths that would not generate undue heat due to resonance waves created in such structures when under the influence of an MRI field generated by an MRI machine. Alternatively, or additionally, portions, or all of the catheter 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 materials, for example, may not be suitable because they may create artifacts in an MRI image. Additionally, all or portions of the catheter, may also be made from a material that the MRI machine can image, as described above. Some materials that exhibit these characteristics include, for example, tungsten, Elgiloy, MP35N, nitinol, and the like, and others.

The present invention should not be considered limited to the particular examples described above, but rather should be understood to cover all aspects of the invention as fairly set out in the attached claims. Various modifications, equivalent processes, as well as numerous structures to which the present invention may be applicable will be readily apparent to those of skill in the art to which the present invention is directed upon review of the instant specification. 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

What is claimed is:
1. A medical device comprising: an elongated inner tubular member including a proximal portion and a distal portion and defining an outer surface and a lumen; and an elongated tubular reinforcing member having an inner surface, the reinforcing member being disposed about the proximal portion of the inner tubular member such that the distal portion of the inner tubular member is free of the reinforcing member, and such that at least a portion of the outer surface of the inner tubular member along the proximal portion is spaced from the inner surface of the reinforcing member.
2. The medical device of claim 1, wherein the distal portion of the inner tubular member includes a tip structure.
3. The medical device of claim 2, wherein the tip structure includes one or more layers of material disposed on the distal portion of the inner tubular member.
4. The medical device of claim 2, wherein the tip structure includes two or more layers of material disposed about distal portion of the inner tubular member.
5. The medical device of claim 2, wherein the tip structure includes a layer of material comprising a reinforcement structure.
6. The medical device of claim 2, wherein the reinforcement structure comprises a coil.
7. The medical device of claim 2, wherein the tip structure includes a layer of polymer material.
8. The medical device of claim 7, wherein the reinforcing member is made of a first material, and the polymer material is more flexible than the first material.
9. The medical device of claim 2, wherein the tip structure includes a coil disposed about the distal portion of the inner tubular member, and a layer of polymer material disposed about the coil.
10. The medical device of claim 1, wherein the medical device includes an atraumatic tip structure disposed on the distal portion of the inner tubular member, and wherein the reinforcing member is made of a first material, and the atraumatic tip structure is made of a second material different from the first material.
11. The medical device of claim 1, wherein the reinforcing member includes a distal end, and the distal portion of the inner tubular member includes a tip structure coupled to the distal portion of the inner tubular member adjacent to the distal end of the reinforcing member.
12. The medical device of claim 1, wherein the distal portion of the inner tubular member has a length in the range of about 1 cm or greater.
13. The medical device of claim 1, wherein the distal portion of the inner tubular member has a length in the range of about 2 cm or greater.
14. The medical device of claim 1, wherein the distal portion of the inner tubular member has a length in the range of about 3 cm or greater.
15. The medical device of claim 1, wherein the inner tubular member comprises polymer material.
16. The medical device of claim 1, wherein the inner tubular member includes two or more layers of polymer material.
17. The medical device of claim 1, wherein the reinforcing member comprises a metal or metal alloy.
18. The medical device of claim 1, wherein the reinforcing member comprises a nickel-titanium alloy.
19. The medical device of claim 18, wherein the reinforcing member comprises a superelastic nickel-titanium alloy.
20. The medical device of claim 1, wherein the reinforcing member comprises a tube including a plurality of apertures defined therein.
21. The medical device of claim 1, wherein the reinforcing member includes a distal region and a proximal region, and wherein the distal region includes a plurality of apertures therein, while the proximal region is free of a plurality of apertures defined therein.
22. The medical device of claim 1, wherein the reinforcing member is disposed over the entire proximal portion of the inner tubular member.
23. The medical device of claim 1, wherein the medical device is a catheter.
24. The medical device of claim 23, wherein the catheter is a microcatheter having an outer diameter in the range of about 1 to about 4 French.
25. The medical device of claim 1, wherein the spacing between the outer surface of the inner tubular member and the inner surface of the reinforcing member forms a space that is unfilled by other structure of the catheter.
26. The medical device of claim 1, wherein the reinforcing member has a total length, and wherein the spacing between the outer surface of the inner tubular member and the inner surface of the reinforcing member forms a space that extends along the reinforcing member in the range of 75% or greater of the total length of the reinforcing member.
27. The medical device of claim 25, wherein the space between the outer surface of the inner tubular member and the inner surface of the reinforcing member is in the range of range of about 0.0002 to about 0.004 inch in size.
28. A medical device comprising: an elongated inner tubular member including a proximal portion and a distal portion and defining an outer surface and a lumen; and a elongated tubular reinforcing member having an outer surface and an inner surface, and including a plurality of apertures defined in the outer surface thereof, the reinforcing member being disposed about the entire length of the proximal portion of the inner tubular member such that the distal portion of the inner tubular member is free of the reinforcing member, and wherein at least a portion of the outer surface of the inner tubular member along the proximal portion is spaced from the inner surface of the reinforcing member such that a space is formed that is unfilled by other structure of the catheter.
29. A catheter comprising: an elongated inner tubular member including a proximal portion and a distal portion and defining an outer surface and a lumen; a elongated tubular reinforcing member having an proximal end and a distal end, and defining an outer surface and an inner surface, and including a plurality of apertures defined in the outer surface, the reinforcing member being disposed about the proximal portion of the inner tubular member such that the distal portion of the inner tubular member is free of the reinforcing member and such that a space is formed between the outer surface of the inner tubular member and the inner surface of the reinforcing member along the proximal portion; and a tip structure coupled to the distal portion of the inner tubular member adjacent the distal end of the reinforcing member.
30. The catheter of claim 29, wherein the tip structure includes one or more layers of material disposed on the distal portion of the inner tubular member.
31. The catheter of claim 29, wherein the tip structure includes a layer of material comprising a reinforcement structure comprising a coil.
32. The catheter of claim 29, wherein the tip structure includes a layer of polymer material.
33. The catheter of claim 29, wherein the tip structure includes a coil disposed about the distal portion of the inner tubular member, and a layer of polymer material disposed about the coil.
34. The catheter of claim 29, wherein the distal portion of the inner tubular member has a length in the range of about 1 cm or greater.
35. The catheter of claim 29, wherein the distal portion of the inner tubular member has a length in the range of about 2 cm or greater.
36. The catheter of claim 29, wherein the reinforcing member includes a distal region and a proximal region, and wherein the distal region includes a plurality of apertures therein, while the proximal region is free of a plurality of apertures defined therein.
37. The catheter of claim 29, wherein the reinforcing member is disposed over the entire proximal portion of the inner tubular member.
38. A method of manufacturing an elongate shaft of a medical device, the method comprising: providing a first elongated tubular member including a proximal portion and a distal portion and defining an outer surface and a lumen; and coupling a elongated tubular reinforcing member about the proximal portion of the inner tubular member such that the distal portion of the inner tubular member is free of the reinforcing member, the elongated tubular reinforcing member having an inner surface, and the elongated tubular reinforcing member being coupled to the first elongated tubular member and such that at least a portion of the outer surface of the inner tubular member along the proximal portion is spaced from the inner surface of the reinforcing member.
39. The method of claim 38, wherein the reinforcing member includes a distal end, and further including coupling a tip structure to the distal portion of the inner tubular member adjacent the distal end of the reinforcing member.
40. The method of claim 39, wherein the tip structure includes one or more layers of material disposed on the distal portion of the inner tubular member.
41. The method of claim 39, wherein the tip structure includes a layer of material comprising a reinforcement structure comprising a coil.
42. The method of claim 39, wherein the tip structure includes a layer of polymer material.
43. The method of claim 39, wherein the tip structure includes a coil disposed about the distal portion of the inner tubular member, and a layer of polymer material disposed about the coil.
44. The method of claim 38, wherein the distal portion of the inner tubular member has a length in the range of about 1 cm or greater.
45. The method of claim 38, wherein the distal portion of the inner tubular member has a length in the range of about 2 cm or greater.
46. The method of claim 38, wherein the reinforcing member includes a distal region and a proximal region, and wherein the distal region includes a plurality of apertures therein, while the proximal region is free of a plurality of apertures defined therein.
47. The method of claim 38, wherein the reinforcing member is disposed over the entire proximal portion of the inner tubular member.
48. A catheter comprising: a first elongated tubular member including a proximal portion and a distal portion and defining an outer surface and a lumen, a means for reinforcing the proximal portion of the inner tubular member such that the distal portion of the inner tubular member is free of the reinforcing means and such that at least a portion of the reinforcing means is spaced from the proximal portion of the inner tubular member; and a means for providing an atraumatic tip on the distal portion of the inner tubular member.
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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2006122155A1 (en) * 2005-05-09 2006-11-16 Boston Scientific Limited Medical device
US9808595B2 (en) 2007-08-07 2017-11-07 Boston Scientific Scimed, Inc Microfabricated catheter with improved bonding structure

Families Citing this family (238)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6413234B1 (en) * 1990-02-02 2002-07-02 Ep Technologies, Inc. Assemblies for creating compound curves in distal catheter regions
EP0814866B1 (en) 1995-03-20 2001-06-20 Medimop Medical Projects Ltd. Fluid control device
US20030069522A1 (en) 1995-12-07 2003-04-10 Jacobsen Stephen J. Slotted medical device
ES2274984T3 (en) * 2001-07-05 2007-06-01 Precision Vascular Systems, Inc. medical device soft tip which can undergo torsion and method to conform.
US7914467B2 (en) 2002-07-25 2011-03-29 Boston Scientific Scimed, Inc. Tubular member having tapered transition for use in a medical device
DE60334122D1 (en) 2002-07-25 2010-10-21 Boston Scient Ltd A medical device for navigation through the anatomy
DE50209306D1 (en) 2002-12-31 2007-03-08 Abbott Lab Vascular Entpr Ltd Catheter with a flexible region between the shank and tip and method for its preparation
US8377035B2 (en) * 2003-01-17 2013-02-19 Boston Scientific Scimed, Inc. Unbalanced reinforcement members for medical device
US7001369B2 (en) * 2003-03-27 2006-02-21 Scimed Life Systems, Inc. Medical device
US7306683B2 (en) * 2003-04-18 2007-12-11 Versitech Limited Shape memory material and method of making the same
US20050015072A1 (en) * 2003-07-15 2005-01-20 Medtronic, Inc. Cannula having buckle resistant apertures
USD669577S1 (en) * 2003-11-05 2012-10-23 Kimberly-Clark Worldwide, Inc. Cannula with band markings
JP3852033B2 (en) * 2003-12-12 2006-11-29 正喜 江刺 Active tube and active tube system
US7824345B2 (en) 2003-12-22 2010-11-02 Boston Scientific Scimed, Inc. Medical device with push force limiter
US7761138B2 (en) * 2004-03-12 2010-07-20 Boston Scientific Scimed, Inc. MRI and X-ray visualization
US7844344B2 (en) 2004-03-30 2010-11-30 Medtronic, Inc. MRI-safe implantable lead
US8235968B2 (en) * 2004-04-13 2012-08-07 Gyrus Acmi, Inc. Atraumatic ureteral access sheath
US8535293B2 (en) * 2004-04-13 2013-09-17 Gyrus Acmi, Inc. Atraumatic ureteral access sheath
US8517921B2 (en) * 2004-04-16 2013-08-27 Gyrus Acmi, Inc. Endoscopic instrument having reduced diameter flexible shaft
WO2005102458A3 (en) * 2004-04-19 2006-04-27 Univ The Board Of Trustees The Airway implant devices and methods of use
US7887529B2 (en) * 2004-04-19 2011-02-15 Boston Scientific Scimed, Inc. Hybrid micro guide catheter
WO2005105014A3 (en) 2004-04-29 2005-12-01 Igor Denenberg Liquid drug medical device
US20050256401A1 (en) * 2004-05-14 2005-11-17 Scion Cardio-Vascular, Inc. Catheter with variable diameter core spacing and associated actuated device
EP1748814A1 (en) * 2004-05-27 2007-02-07 Abbott Laboratories Catheter having main body portion with coil-defined guidewire passage
US7815627B2 (en) * 2004-05-27 2010-10-19 Abbott Laboratories Catheter having plurality of stiffening members
US7794448B2 (en) 2004-05-27 2010-09-14 Abbott Laboratories Multiple lumen catheter and method of making same
US7785318B2 (en) 2004-05-27 2010-08-31 Abbott Laboratories Catheter having plurality of stiffening members
US7658723B2 (en) 2004-05-27 2010-02-09 Abbott Laboratories Catheter having plurality of stiffening members
EP1807144A1 (en) * 2004-09-14 2007-07-18 William, a Cook Australia Pty. Ltd. Large diameter sheath
US7785439B2 (en) 2004-09-29 2010-08-31 Abbott Laboratories Vascular Enterprises Limited Method for connecting a catheter balloon with a catheter shaft of a balloon catheter
DE602004010276D1 (en) * 2004-11-10 2008-01-03 Creganna Technologies Ltd Einführkatheteranordnung for stents
US20090118577A9 (en) * 2005-12-13 2009-05-07 Gyrus Acmi, Inc. Medical device made with a super alloy
US7410462B2 (en) * 2004-12-13 2008-08-12 Gyrus Acmi, Inc. Hermetic endoscope assemblage
DE102005011656A1 (en) * 2005-03-14 2006-09-21 Breeze Medical, Inc., Boca Raton System for delivering an agent into a blood vessel
US20060282112A1 (en) * 2005-06-09 2006-12-14 Stephen Griffin Method and apparatus for enhanced electrolytic detachment
US20070030880A1 (en) * 2005-08-04 2007-02-08 Kaz, Incorporated Gold tip thermometer
US8070739B2 (en) 2005-08-11 2011-12-06 Medimop Medical Projects Ltd. Liquid drug transfer devices for failsafe correct snap fitting onto medicinal vials
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
US8292827B2 (en) * 2005-12-12 2012-10-23 Boston Scientific Scimed, Inc. Micromachined medical devices
US9901731B2 (en) * 2006-01-31 2018-02-27 Medtronic, Inc. Medical electrical lead having improved inductance
US20070179582A1 (en) * 2006-01-31 2007-08-02 Marshall Mark T Polymer reinforced coil conductor for torque transmission
WO2007095751A1 (en) * 2006-02-22 2007-08-30 Strauss Bradley H Guide-wire sleeve for facilitation of lesion crossing
US8025693B2 (en) * 2006-03-01 2011-09-27 Boston Scientific Scimed, Inc. Stent-graft having flexible geometries and methods of producing the same
US20080097397A1 (en) * 2006-06-08 2008-04-24 Vrba Anthony C Vascular introducer sheath
US8021352B2 (en) 2006-08-23 2011-09-20 Codman & Shurtleff, Inc. Unfused catheter body feature and methods of manufacture
US7857008B2 (en) * 2006-08-24 2010-12-28 Boston Scientific Scimed, Inc. Medical device coating configuration and method for improved lubricity and durability
US8728010B2 (en) * 2006-08-24 2014-05-20 Boston Scientific Scimed, Inc. Elongate medical device including deformable distal end
US8419658B2 (en) * 2006-09-06 2013-04-16 Boston Scientific Scimed, Inc. Medical device including structure for crossing an occlusion in a vessel
JP2010503484A (en) * 2006-09-13 2010-02-04 ボストン サイエンティフィック リミテッド Transverse guide wire
US8574219B2 (en) * 2006-09-18 2013-11-05 Boston Scientific Scimed, Inc. Catheter shaft including a metallic tapered region
US20080172037A1 (en) * 2006-11-01 2008-07-17 Percutaneous Systems, Inc. Catheter with adjustable column stability and methods for its use
US7610101B2 (en) 2006-11-30 2009-10-27 Cardiac Pacemakers, Inc. RF rejecting lead
US20080132933A1 (en) * 2006-11-30 2008-06-05 Medtronic, Inc. Flexible introducer
US8556914B2 (en) * 2006-12-15 2013-10-15 Boston Scientific Scimed, Inc. Medical device including structure for crossing an occlusion in a vessel
US8961551B2 (en) 2006-12-22 2015-02-24 The Spectranetics Corporation Retractable separating systems and methods
US9028520B2 (en) 2006-12-22 2015-05-12 The Spectranetics Corporation Tissue separating systems and methods
US7824270B2 (en) * 2007-01-23 2010-11-02 C-Flex Bearing Co., Inc. Flexible coupling
US7655004B2 (en) 2007-02-15 2010-02-02 Ethicon Endo-Surgery, Inc. Electroporation ablation apparatus, system, and method
CN101636837B (en) * 2007-03-23 2011-07-27 富士通株式会社 Electronic device, electronic apparatus mounting electronic device, article mounting electronic device, and method for manufacturing electronic device
WO2008126090A1 (en) 2007-04-17 2008-10-23 Medimop Medical Projects Ltd Fluid control device with manually depressed actuator
US20080262474A1 (en) * 2007-04-20 2008-10-23 Boston Scientific Scimed, Inc. Medical device
US8483842B2 (en) 2007-04-25 2013-07-09 Medtronic, Inc. Lead or lead extension having a conductive body and conductive body contact
US8075572B2 (en) 2007-04-26 2011-12-13 Ethicon Endo-Surgery, Inc. Surgical suturing apparatus
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
US20090036832A1 (en) * 2007-08-03 2009-02-05 Boston Scientific Scimed, Inc. Guidewires and methods for manufacturing guidewires
US20090043228A1 (en) * 2007-08-06 2009-02-12 Boston Scientific Scimed, Inc. Laser shock peening of medical devices
US8821477B2 (en) 2007-08-06 2014-09-02 Boston Scientific Scimed, Inc. Alternative micromachined structures
US8568410B2 (en) 2007-08-31 2013-10-29 Ethicon Endo-Surgery, Inc. Electrical ablation surgical instruments
US8377036B2 (en) * 2007-09-14 2013-02-19 Avalon Laboratories, Inc. Cannula reinforcing band and method
CN101918074B (en) 2007-09-18 2013-02-27 麦迪麦珀医疗工程有限公司 Medicament mixing and injection apparatus
US9034007B2 (en) 2007-09-21 2015-05-19 Insera Therapeutics, Inc. Distal embolic protection devices with a variable thickness microguidewire and methods for their use
US8016809B2 (en) 2007-09-25 2011-09-13 Medimop Medical Projects Ltd. Liquid drug delivery devices for use with syringes with widened distal tips
US20090112059A1 (en) 2007-10-31 2009-04-30 Nobis Rudolph H Apparatus and methods for closing a gastrotomy
US8480657B2 (en) 2007-10-31 2013-07-09 Ethicon Endo-Surgery, Inc. Detachable distal overtube section and methods for forming a sealable opening in the wall of an organ
US20090118675A1 (en) * 2007-11-02 2009-05-07 Boston Scientific Scimed, Inc. Elongate medical device with a shapeable tip
US7841994B2 (en) 2007-11-02 2010-11-30 Boston Scientific Scimed, Inc. Medical device for crossing an occlusion in a vessel
US20090131912A1 (en) * 2007-11-15 2009-05-21 Wright-Ahn Technologies, Llc Variable Stiffness Guidewire Systems
US8579897B2 (en) 2007-11-21 2013-11-12 Ethicon Endo-Surgery, Inc. Bipolar forceps
US8262655B2 (en) 2007-11-21 2012-09-11 Ethicon Endo-Surgery, Inc. Bipolar forceps
JP5073829B2 (en) 2007-12-06 2012-11-14 カーディアック ペースメイカーズ, インコーポレイテッド Implantable lead having a variable coil conductor pitch
US20090157047A1 (en) * 2007-12-13 2009-06-18 Boston Scientific Scimed, Inc. Medical device coatings and methods of forming such coatings
US20100286626A1 (en) * 2007-12-21 2010-11-11 Petersen Scott R Longitudinally incompressible, laterally flexible interior shaft for catheter
US8431057B2 (en) * 2007-12-30 2013-04-30 St. Jude Medical, Atrial Fibrillation Division, Inc. Catheter shaft and method of its manufacture
US8460213B2 (en) 2008-01-03 2013-06-11 Boston Scientific Scimed, Inc. Cut tubular members for a medical device and methods for making and using the same
EP2249920B1 (en) 2008-02-06 2015-07-01 Cardiac Pacemakers, Inc. Lead with mri compatible design features
US8262680B2 (en) 2008-03-10 2012-09-11 Ethicon Endo-Surgery, Inc. Anastomotic device
US9037263B2 (en) 2008-03-12 2015-05-19 Medtronic, Inc. System and method for implantable medical device lead shielding
US8376961B2 (en) 2008-04-07 2013-02-19 Boston Scientific Scimed, Inc. Micromachined composite guidewire structure with anisotropic bending properties
US20090270841A1 (en) * 2008-04-24 2009-10-29 Cook Incorporated Catheters
US8103360B2 (en) 2008-05-09 2012-01-24 Foster Arthur J Medical lead coil conductor with spacer element
US8070759B2 (en) 2008-05-30 2011-12-06 Ethicon Endo-Surgery, Inc. Surgical fastening device
US8114072B2 (en) 2008-05-30 2012-02-14 Ethicon Endo-Surgery, Inc. Electrical ablation device
US8317806B2 (en) 2008-05-30 2012-11-27 Ethicon Endo-Surgery, Inc. Endoscopic suturing tension controlling and indication devices
US8771260B2 (en) 2008-05-30 2014-07-08 Ethicon Endo-Surgery, Inc. Actuating and articulating surgical device
US8679003B2 (en) 2008-05-30 2014-03-25 Ethicon Endo-Surgery, Inc. Surgical device and endoscope including same
US8652150B2 (en) 2008-05-30 2014-02-18 Ethicon Endo-Surgery, Inc. Multifunction surgical device
US8906035B2 (en) 2008-06-04 2014-12-09 Ethicon Endo-Surgery, Inc. Endoscopic drop off bag
US8403926B2 (en) 2008-06-05 2013-03-26 Ethicon Endo-Surgery, Inc. Manually articulating devices
US8361112B2 (en) 2008-06-27 2013-01-29 Ethicon Endo-Surgery, Inc. Surgical suture arrangement
US20100010294A1 (en) * 2008-07-10 2010-01-14 Ethicon Endo-Surgery, Inc. Temporarily positionable medical devices
US8888792B2 (en) 2008-07-14 2014-11-18 Ethicon Endo-Surgery, Inc. Tissue apposition clip application devices and methods
US8262563B2 (en) * 2008-07-14 2012-09-11 Ethicon Endo-Surgery, Inc. Endoscopic translumenal articulatable steerable overtube
US20100016937A1 (en) * 2008-07-18 2010-01-21 Yousef Alkhatib Twisting Bifurcation Delivery System
US8211125B2 (en) * 2008-08-15 2012-07-03 Ethicon Endo-Surgery, Inc. Sterile appliance delivery device for endoscopic procedures
US20100048758A1 (en) * 2008-08-22 2010-02-25 Boston Scientific Scimed, Inc. Lubricious coating composition for devices
US8529563B2 (en) 2008-08-25 2013-09-10 Ethicon Endo-Surgery, Inc. Electrical ablation devices
US8241204B2 (en) 2008-08-29 2012-08-14 Ethicon Endo-Surgery, Inc. Articulating end cap
US8480689B2 (en) 2008-09-02 2013-07-09 Ethicon Endo-Surgery, Inc. Suturing device
US8409200B2 (en) 2008-09-03 2013-04-02 Ethicon Endo-Surgery, Inc. Surgical grasping device
US8114119B2 (en) 2008-09-09 2012-02-14 Ethicon Endo-Surgery, Inc. Surgical grasping device
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
US8337394B2 (en) 2008-10-01 2012-12-25 Ethicon Endo-Surgery, Inc. Overtube with expandable tip
US8157834B2 (en) 2008-11-25 2012-04-17 Ethicon Endo-Surgery, Inc. Rotational coupling device for surgical instrument with flexible actuators
US9072873B2 (en) * 2009-04-03 2015-07-07 Scientia Vascular, Llc Micro-fabricated guidewire devices having elastomeric compositions
US9616195B2 (en) * 2009-04-03 2017-04-11 Scientia Vascular, Llc Micro-fabricated catheter devices having varying diameters
CN102639303B (en) 2008-12-08 2015-09-30 血管科学有限公司 A micro-cutter cuts formed in the product
US20100256602A1 (en) * 2009-04-03 2010-10-07 Scientia Vascular, Llc Micro-fabricated Guidewire Devices Formed With Hybrid Materials
US9067333B2 (en) 2009-04-03 2015-06-30 Scientia Vascular, Llc Micro-fabricated guidewire devices having elastomeric fill compositions
US20100256528A1 (en) * 2009-04-03 2010-10-07 Scientia Vascular, Llc Micro-fabricated Guidewire Devices Having Varying Diameters
US20100256603A1 (en) * 2009-04-03 2010-10-07 Scientia Vascular, Llc Micro-fabricated Catheter Devices Formed Having Elastomeric Fill Compositions
US8795254B2 (en) * 2008-12-10 2014-08-05 Boston Scientific Scimed, Inc. Medical devices with a slotted tubular member having improved stress distribution
US8172772B2 (en) * 2008-12-11 2012-05-08 Ethicon Endo-Surgery, Inc. Specimen retrieval device
US8361066B2 (en) 2009-01-12 2013-01-29 Ethicon Endo-Surgery, Inc. Electrical ablation devices
US8828031B2 (en) 2009-01-12 2014-09-09 Ethicon Endo-Surgery, Inc. Apparatus for forming an anastomosis
US9226772B2 (en) 2009-01-30 2016-01-05 Ethicon Endo-Surgery, Inc. Surgical device
US8252057B2 (en) 2009-01-30 2012-08-28 Ethicon Endo-Surgery, Inc. Surgical access device
EP2403440A1 (en) 2009-02-20 2012-01-11 Boston Scientific Scimed, Inc. Balloon catheter for placemnt of a stent in a bifurcated vessel
US20100227697A1 (en) * 2009-03-04 2010-09-09 C-Flex Bearing Co., Inc. Flexible coupling
US9084883B2 (en) 2009-03-12 2015-07-21 Cardiac Pacemakers, Inc. Thin profile conductor assembly for medical device leads
USD641080S1 (en) 2009-03-31 2011-07-05 Medimop Medical Projects Ltd. Medical device having syringe port with locking mechanism
US20120035696A1 (en) 2009-04-30 2012-02-09 Medtronic, Inc. Termination of a shield within an implantable medical lead
US8880193B1 (en) 2009-05-22 2014-11-04 Advanced Bionics, Llc Cochlear electrode array
WO2010151698A3 (en) * 2009-06-24 2011-03-24 Shifamed, Llc Steerable medical delivery devices and methods of use
JP5542926B2 (en) 2009-06-26 2014-07-09 カーディアック ペースメイカーズ, インコーポレイテッド Medical device lead containing conductor assembly of reduced single-wire coil heating by mri with improved torque transmission performance
US8712554B2 (en) 2009-07-21 2014-04-29 Advanced Bionics Integrated wire carrier for electrode array
US8512232B2 (en) * 2009-09-08 2013-08-20 Gyrus Acmi, Inc. Endoscopic illumination system, assembly and methods for staged illumination of different target areas
WO2011039747A1 (en) 2009-10-01 2011-04-07 Medimop Medical Projects Ltd Vial assemblage with vial and pre-attached fluid transfer device
US8335572B2 (en) * 2009-10-08 2012-12-18 Cardiac Pacemakers, Inc. Medical device lead including a flared conductive coil
US20110093009A1 (en) * 2009-10-16 2011-04-21 Ethicon Endo-Surgery, Inc. Otomy closure device
US9254380B2 (en) 2009-10-19 2016-02-09 Cardiac Pacemakers, Inc. MRI compatible tachycardia lead
US8608652B2 (en) 2009-11-05 2013-12-17 Ethicon Endo-Surgery, Inc. Vaginal entry surgical devices, kit, system, and method
EP2490648B1 (en) 2009-11-12 2014-05-07 Medimop Medical Projects Ltd. Inline liquid drug medical devices with linear displaceable sliding flow control member
CN102985047B (en) 2009-11-12 2015-07-01 麦迪麦珀医疗工程有限公司 Fluid transfer devices with sealing arrangement
US8137293B2 (en) 2009-11-17 2012-03-20 Boston Scientific Scimed, Inc. Guidewires including a porous nickel-titanium alloy
US8519300B2 (en) * 2009-12-11 2013-08-27 Cardiac Pacemakers, Inc. Method of laser welding a hub to a catheter shaft
US8353487B2 (en) * 2009-12-17 2013-01-15 Ethicon Endo-Surgery, Inc. User interface support devices for endoscopic surgical instruments
US8496574B2 (en) 2009-12-17 2013-07-30 Ethicon Endo-Surgery, Inc. Selectively positionable camera for surgical guide tube assembly
US8506564B2 (en) 2009-12-18 2013-08-13 Ethicon Endo-Surgery, Inc. Surgical instrument comprising an electrode
US9028483B2 (en) 2009-12-18 2015-05-12 Ethicon Endo-Surgery, Inc. Surgical instrument comprising an electrode
US20110160680A1 (en) * 2009-12-29 2011-06-30 Cook Incorporated Wire guide with cannula
WO2011081709A1 (en) * 2009-12-30 2011-07-07 Cardiac Pacemakers, Inc. Mri-conditionally safe medical device lead
JP5542217B2 (en) 2009-12-31 2014-07-09 カーディアック ペースメイカーズ, インコーポレイテッド Secure leads conditionally mri comprising a multilayer conductor
US8391994B2 (en) 2009-12-31 2013-03-05 Cardiac Pacemakers, Inc. MRI conditionally safe lead with low-profile multi-layer conductor for longitudinal expansion
US9005198B2 (en) * 2010-01-29 2015-04-14 Ethicon Endo-Surgery, Inc. Surgical instrument comprising an electrode
CN102711712B (en) 2010-02-24 2014-08-13 麦迪麦珀医疗工程有限公司 Fluid transfer assembly with venting arrangement
CN102781396B (en) 2010-02-24 2015-01-07 麦迪麦珀医疗工程有限公司 Liquid drug transfer device with vented vial adapter
US20110238041A1 (en) * 2010-03-24 2011-09-29 Chestnut Medical Technologies, Inc. Variable flexibility catheter
EP2552530A1 (en) 2010-03-31 2013-02-06 Boston Scientific Scimed, Inc. Guidewire with a flexural rigidity profile
US20120041411A1 (en) * 2010-04-19 2012-02-16 Micrus Endovascular Llc Low profile guiding catheter for neurovascular applications
US9033869B2 (en) 2010-05-27 2015-05-19 Advanced Bionics, Llc Cochlear lead
US9037267B2 (en) 2010-05-27 2015-05-19 Advanced Bionics Llc Cochlear lead
US8473075B2 (en) 2010-06-25 2013-06-25 Advanced Bionics Cochlear implant system with removable stylet
US8825181B2 (en) 2010-08-30 2014-09-02 Cardiac Pacemakers, Inc. Lead conductor with pitch and torque control for MRI conditionally safe use
USD669980S1 (en) 2010-10-15 2012-10-30 Medimop Medical Projects Ltd. Vented vial adapter
US9084610B2 (en) 2010-10-21 2015-07-21 Medtronic Ardian Luxembourg S.A.R.L. Catheter apparatuses, systems, and methods for renal neuromodulation
WO2012061161A1 (en) 2010-10-25 2012-05-10 Medtronic Ardian Luxembourg S.A.R.L. Catheter apparatuses having multi-electrode arrays for renal neuromodulation and associated systems and methods
WO2012061935A1 (en) * 2010-11-09 2012-05-18 Opsens Inc. Guidewire with internal pressure sensor
JP5575990B2 (en) 2010-11-14 2014-08-20 メディモップ・メディカル・プロジェクツ・リミテッド Inline liquid medical device having a rotary flow control member
US8795202B2 (en) 2011-02-04 2014-08-05 Boston Scientific Scimed, Inc. Guidewires and methods for making and using the same
US9314620B2 (en) 2011-02-28 2016-04-19 Ethicon Endo-Surgery, Inc. Electrical ablation devices and methods
US9233241B2 (en) 2011-02-28 2016-01-12 Ethicon Endo-Surgery, Inc. Electrical ablation devices and methods
US9254169B2 (en) 2011-02-28 2016-02-09 Ethicon Endo-Surgery, Inc. Electrical ablation devices and methods
WO2012125785A1 (en) 2011-03-17 2012-09-20 Ethicon Endo-Surgery, Inc. Hand held surgical device for manipulating an internal magnet assembly within a patient
EP2680806B1 (en) 2011-04-17 2015-04-15 Medimop Medical Projects Ltd Liquid drug transfer assembly
CA2833387A1 (en) 2011-05-03 2012-11-08 Shifamed Holdings, Llc Steerable delivery sheaths
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
EP2572749A3 (en) 2011-09-23 2013-04-03 Covidien LP Distal access balloon guide catheter
DK2736478T3 (en) 2011-10-11 2016-02-15 Medimop Medical Projects Ltd A valve arrangement for use with a liquid container, and a medicament vial
EP2773422B1 (en) 2011-11-04 2015-11-04 Cardiac Pacemakers, Inc. Implantable medical device lead including inner coil reverse-wound relative to defibrillation coil
WO2013085749A1 (en) * 2011-12-05 2013-06-13 Stryker Corporation Reinforced elongate medical device and method of manufacture
WO2013109318A1 (en) * 2012-01-17 2013-07-25 Boston Scientific Scimed, Inc. Renal nerve modulation devices and methods for making and using the same
USD737436S1 (en) 2012-02-13 2015-08-25 Medimop Medical Projects Ltd. Liquid drug reconstitution assembly
USD720451S1 (en) 2012-02-13 2014-12-30 Medimop Medical Projects Ltd. Liquid drug transfer assembly
USD674088S1 (en) 2012-02-13 2013-01-08 Medimop Medical Projects Ltd. Vial adapter
US8986199B2 (en) 2012-02-17 2015-03-24 Ethicon Endo-Surgery, Inc. Apparatus and methods for cleaning the lens of an endoscope
WO2013150538A1 (en) 2012-04-05 2013-10-10 Medimop Medical Projects Ltd Fluid transfer devices having cartridge port with cartridge ejection arrangement
US8961550B2 (en) 2012-04-17 2015-02-24 Indian Wells Medical, Inc. Steerable endoluminal punch
US9463317B2 (en) 2012-04-19 2016-10-11 Medtronic, Inc. Paired medical lead bodies with braided conductive shields having different physical parameter values
US8825179B2 (en) 2012-04-20 2014-09-02 Cardiac Pacemakers, Inc. Implantable medical device lead including a unifilar coiled cable
CN107374723A (en) 2012-05-11 2017-11-24 美敦力Af卢森堡有限责任公司 Catheter
US9427255B2 (en) 2012-05-14 2016-08-30 Ethicon Endo-Surgery, Inc. Apparatus for introducing a steerable camera assembly into a patient
US8954168B2 (en) 2012-06-01 2015-02-10 Cardiac Pacemakers, Inc. Implantable device lead including a distal electrode assembly with a coiled component
US9078662B2 (en) 2012-07-03 2015-07-14 Ethicon Endo-Surgery, Inc. Endoscopic cap electrode and method for using the same
WO2014011865A8 (en) 2012-07-13 2014-03-06 Boston Scientific Scimed, Inc. Occlusion device for an atrial appendage
US20140025085A1 (en) * 2012-07-18 2014-01-23 Boston Scientific Scimed, Inc. Catheter having radially expandable shaft
US9545290B2 (en) 2012-07-30 2017-01-17 Ethicon Endo-Surgery, Inc. Needle probe guide
US9572623B2 (en) 2012-08-02 2017-02-21 Ethicon Endo-Surgery, Inc. Reusable electrode and disposable sheath
US9277957B2 (en) 2012-08-15 2016-03-08 Ethicon Endo-Surgery, Inc. Electrosurgical devices and methods
JP5808512B2 (en) 2012-08-26 2015-11-10 メディモップ・メディカル・プロジェクツ・リミテッド Liquid transfer device using a manual rotation for the two flow communication process operation
CN105769561A (en) 2012-08-26 2016-07-20 麦迪麦珀医疗工程有限公司 Liquid Drug Transfer Devices
WO2014036529A1 (en) 2012-08-31 2014-03-06 Cardiac Pacemakers, Inc. Mri compatible lead coil
JP5868555B2 (en) 2012-09-13 2016-02-24 メディモップ・メディカル・プロジェクツ・リミテッド Telescopic female vial adapter
US9724122B2 (en) 2012-09-14 2017-08-08 The Spectranetics Corporation Expandable lead jacket
EP2908903B1 (en) 2012-10-18 2016-08-31 Cardiac Pacemakers, Inc. Inductive element for providing mri compatibility in an implantable medical device lead
USD734868S1 (en) 2012-11-27 2015-07-21 Medimop Medical Projects Ltd. Drug vial adapter with downwardly depending stopper
US9291663B2 (en) 2013-03-13 2016-03-22 The Spectranetics Corporation Alarm for lead insulation abnormality
US9883885B2 (en) 2013-03-13 2018-02-06 The Spectranetics Corporation System and method of ablative cutting and pulsed vacuum aspiration
US9283040B2 (en) 2013-03-13 2016-03-15 The Spectranetics Corporation Device and method of ablative cutting with helical tip
US9456872B2 (en) 2013-03-13 2016-10-04 The Spectranetics Corporation Laser ablation catheter
US9668765B2 (en) 2013-03-15 2017-06-06 The Spectranetics Corporation Retractable blade for lead removal device
USD770616S1 (en) 2015-02-20 2016-11-01 The Spectranetics Corporation Medical device handle
EP2967634A4 (en) 2013-03-15 2017-02-08 Spectranetics Corp Surgical instrument for removing an implanted object
US9314324B2 (en) 2013-07-29 2016-04-19 Insera Therapeutics, Inc. Vascular treatment devices and methods
US8715314B1 (en) 2013-03-15 2014-05-06 Insera Therapeutics, Inc. Vascular treatment measurement methods
US8679150B1 (en) 2013-03-15 2014-03-25 Insera Therapeutics, Inc. Shape-set textile structure based mechanical thrombectomy methods
USD765243S1 (en) 2015-02-20 2016-08-30 The Spectranetics Corporation Medical device handle
US9918737B2 (en) 2013-03-15 2018-03-20 The Spectranetics Corporation Medical device for removing an implanted object
US8715315B1 (en) 2013-03-15 2014-05-06 Insera Therapeutics, Inc. Vascular treatment systems
DK2986267T3 (en) 2013-04-14 2017-09-11 Medimop Medical Projects Ltd A medicament container closure for mounting on the open-topped container drug to form a drug reconstruction device for use with a needleless syringe
USD765837S1 (en) 2013-08-07 2016-09-06 Medimop Medical Projects Ltd. Liquid transfer device with integral vial adapter
USD767124S1 (en) 2013-08-07 2016-09-20 Medimop Medical Projects Ltd. Liquid transfer device with integral vial adapter
US9782186B2 (en) 2013-08-27 2017-10-10 Covidien Lp Vascular intervention system
US9827126B2 (en) 2013-08-27 2017-11-28 Covidien Lp Delivery of medical devices
US20150099997A1 (en) * 2013-10-03 2015-04-09 Oz Cabiri Steering tool
US20150216533A1 (en) * 2014-02-06 2015-08-06 Boston Scientific Scimed, Inc. Occlusion device
US9504821B2 (en) 2014-02-26 2016-11-29 Cardiac Pacemakers, Inc. Construction of an MRI-safe tachycardia lead
WO2015137098A1 (en) * 2014-03-14 2015-09-17 テルモ株式会社 Medical tube
US9901706B2 (en) 2014-04-11 2018-02-27 Boston Scientific Scimed, Inc. Catheters and catheter shafts
USD757933S1 (en) 2014-09-11 2016-05-31 Medimop Medical Projects Ltd. Dual vial adapter assemblage
EP3253301A1 (en) 2015-02-06 2017-12-13 Boston Scientific Scimed, Inc. Occlusion devices
US9768664B2 (en) 2015-05-21 2017-09-19 The Boeing Company Balanced eccentric gear design and method
WO2017007678A1 (en) 2015-07-07 2017-01-12 Boston Scientific Scimed, Inc. Methods and devices for maintaining an open pathway in a vessel
US20170086800A1 (en) 2015-09-25 2017-03-30 Boston Scientific Scimed, Inc. Methods and devices for tissue biopsy
USD801522S1 (en) 2015-11-09 2017-10-31 Medimop Medical Projects Ltd. Fluid transfer assembly
US20170143943A1 (en) 2015-11-20 2017-05-25 Boston Scientific Corporation Balloon catheter

Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5238004A (en) 1990-04-10 1993-08-24 Boston Scientific Corporation High elongation linear elastic guidewire
US5507766A (en) * 1993-01-26 1996-04-16 Terumo Kabushiki Kaisha Vascular dilatation instrument and catheter
EP0812599A2 (en) * 1991-05-07 1997-12-17 Target Therapeutics, Inc. Catheter guide wire
US5772609A (en) 1993-05-11 1998-06-30 Target Therapeutics, Inc. Guidewire with variable flexibility due to polymeric coatings
US6139510A (en) 1994-05-11 2000-10-31 Target Therapeutics Inc. Super elastic alloy guidewire
US20020013540A1 (en) 1999-12-22 2002-01-31 Jacobsen Stephen C. Coronary guidewire system
US6428489B1 (en) 1995-12-07 2002-08-06 Precision Vascular Systems, Inc. Guidewire system
US20030009208A1 (en) * 2001-07-05 2003-01-09 Precision Vascular Systems, Inc. Torqueable soft tip medical device and method of usage
US6508803B1 (en) 1998-11-06 2003-01-21 Furukawa Techno Material Co., Ltd. Niti-type medical guide wire and method of producing the same

Family Cites Families (351)

* 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
US3322984A (en) 1963-05-10 1967-05-30 Bendix Corp Nutation motor or generator
US3363470A (en) 1964-07-20 1968-01-16 Raphael O. Yavne Accelerometer
US3334523A (en) * 1965-03-23 1967-08-08 John D Rieser Pulleys for conveyors and mountings
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
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
FR2280856B1 (en) 1974-09-03 1979-05-25 Statni Vyzkumny Ustav Material
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
US4215703A (en) 1978-08-29 1980-08-05 Willson James K V Variable stiffness guide wire
JPS6122752B2 (en) 1978-12-28 1986-06-02 Matsushita Electric Ind Co Ltd
US4318402A (en) * 1979-07-12 1982-03-09 Critikon, Inc Liquid infusion catheter assembly
US4330725A (en) 1980-03-10 1982-05-18 Morgan Actuators, Inc. Nutating motor coupling
DE3029907A1 (en) 1980-08-07 1982-03-18 Hoechst Ag A continuous process and apparatus for producing a vinyl chloride polymer in aqueous suspension
JPS6223361B2 (en) 1980-09-04 1987-05-22 Pioneer Electronic Corp
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
FR2515859B1 (en) 1981-10-29 1983-12-23 Crouzet Sa
US4476754A (en) 1981-12-07 1984-10-16 Ducret Lucien C Automatic cable measuring and cutting machine
DE3363666D1 (en) 1982-02-26 1986-07-03 Unilever Plc Multi-kilo pack, Primarily for detergent powder
US4545390A (en) 1982-09-22 1985-10-08 C. R. Bard, Inc. Steerable guide wire for balloon dilatation procedure
US4547192A (en) * 1982-11-12 1985-10-15 Superior Plastic Products Corp. Gastroenteric feeding tube
DE3245958A1 (en) 1982-12-11 1984-06-14 Battelle Institut E V laser assembly
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) Accelerometers electrostatic suspension
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
JPS6091858A (en) 1983-10-21 1985-05-23 Yaskawa Electric Mfg Co Ltd Electromagnetic drive device using permanent magnet
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
JPH065981B2 (en) 1984-07-10 1994-01-19 国際技術開発株式会社 Mode - data
US4580551A (en) 1984-11-02 1986-04-08 Warner-Lambert Technologies, Inc. Flexible plastic tube for endoscopes and the like
JPH0519156B2 (en) 1984-11-05 1993-03-15 Tokyo Shibaura Electric Co
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 Dr Cramer Bernhard M Steerable catheters for Fuehrungsdraht
JPS6223361A (en) 1985-07-22 1987-01-31 Takashi Hosokawa Motor actuator
US4998923A (en) 1988-08-11 1991-03-12 Advanced Cardiovascular Systems, Inc. Steerable dilatation catheter
JPH0669286B2 (en) 1985-10-14 1994-08-31 株式会社安川電機 Rolling element type motor
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
JPS62299277A (en) 1986-06-20 1987-12-26 Toray Industries Guide wire
US4867173A (en) 1986-06-30 1989-09-19 Meadox Surgimed A/S Steerable guidewire
DE3621967A1 (en) 1986-07-01 1988-01-14 Heinrich Josef Lettmann Pipe-shaped pump unit with drive motor
US4922777A (en) 1986-09-05 1990-05-08 Contour Saws, Inc. Band saw for cutting shaped pieces of bar stock
DE3633691C1 (en) 1986-10-03 1987-07-23 Keuro Maschb Gmbh & Co Kg An apparatus for feeding stangenfoermigen Werkstueckmaterials at a cut-off 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 富士電機株式会社 Vertical axis mill drive
US5250069A (en) 1987-02-27 1993-10-05 Terumo Kabushiki Kaisha Catheter equipped with expansible member and production method thereof
JPS63217966A (en) 1987-03-04 1988-09-12 Shinko Electric Co Ltd Variable air-gap type motor
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
US4875489A (en) 1987-08-14 1989-10-24 Advanced Cardiovascular Systems, Inc. Extendable guidewire
DE3889041T2 (en) 1987-09-02 1994-10-27 Igen Inc Production of Immunonähe catalysts.
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
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
DE3801514C2 (en) 1988-01-20 1989-11-02 Gebr. Schmidt Fabrik Fuer Feinmechanik, 7742 St Georgen, De
DE3903133A1 (en) 1988-02-04 1989-08-31 Amada Co Werkstueckbearbeitbarkeitsdetektionsverfahren and method for cutting edit a werkstuecks with the help of a cutting processing machine under application of this procedure
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
DE3829603A1 (en) 1988-09-01 1990-03-15 Kontron Holding Ag Ultrasound endoscope device
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
CA1322628C (en) * 1988-10-04 1993-10-05 Richard A. Schatz Expandable intraluminal graft
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
DE8900077U1 (en) 1989-01-04 1990-05-17 Baker, Susan, London, Gb
US5480382A (en) * 1989-01-09 1996-01-02 Pilot Cardiovascular 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
US5063935A (en) 1989-04-27 1991-11-12 C. R. Bard, Inc. Catheter guidewire with varying radiopacity
US4964409A (en) 1989-05-11 1990-10-23 Advanced Cardiovascular Systems, Inc. Flexible hollow guiding member with means for fluid communication therethrough
US4953553A (en) * 1989-05-11 1990-09-04 Advanced Cardiovascular Systems, Inc. Pressure monitoring guidewire with a flexible distal portion
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
JPH03122850A (en) 1989-10-06 1991-05-24 Nec Corp Magneto-optical recording medium
US5256144A (en) 1989-11-02 1993-10-26 Danforth Biomedical, Inc. Low profile, high performance interventional catheters
DE69104349T2 (en) 1990-02-14 1995-05-24 Endevco Corp Surface mount piezoceramic accelerometer and method for its production.
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
US5059177A (en) 1990-04-19 1991-10-22 Cordis Corporation Triple lumen balloon catheter
US5147317A (en) 1990-06-04 1992-09-15 C.R. Bard, Inc. Low friction varied radiopacity guidewire
DE9190089U1 (en) 1990-06-11 1993-02-11 Schneider (Usa) Inc., Plymouth, Minn., Us
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
DE69129539D1 (en) 1990-08-29 1998-07-09 Advanced Cardiovascular System Two spiral springs guidewire with strahlundurchlässiger 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
US5158537A (en) 1990-10-29 1992-10-27 Alza Corporation Iontophoretic delivery device and method of hydrating same
DE69129098T2 (en) 1990-12-18 1998-09-17 Advanced Cardiovascular System A method for producing a super-elastic guide member
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
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
US5329923A (en) 1991-02-15 1994-07-19 Lundquist Ingemar H Torquable catheter
CA2061215A1 (en) 1991-02-15 1992-08-16 Ingemar H. Lundquist Torquable catheter and method
US5315996A (en) 1991-02-15 1994-05-31 Lundquist Ingemar H Torquable catheter and method
US5228441A (en) 1991-02-15 1993-07-20 Lundquist Ingemar H Torquable catheter and method
US5254107A (en) 1991-03-06 1993-10-19 Cordis Corporation Catheter having extended braid reinforced transitional tip
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
US5221270A (en) * 1991-06-28 1993-06-22 Cook Incorporated Soft tip guiding catheter
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
CA2073750C (en) 1991-07-18 1996-11-12 Toshiaki Yutori Catheter guide wire and catheter
JPH09507391A (en) * 1991-07-24 1997-07-29 アドヴァンスト・カーディオヴァスキュラー・システムズ・インコーポレイテッド Low-profile perfusion format dilatation catheter
US5630806A (en) 1991-08-13 1997-05-20 Hudson International Conductors Spiral wrapped medical tubing
EP0680351B1 (en) 1991-09-05 1998-08-05 Mayo Foundation For Medical Education And Research 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
US5741429A (en) 1991-09-05 1998-04-21 Cardia Catheter Company 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
US5205830A (en) 1991-11-12 1993-04-27 Arrow International Investment Corporation Catheter assembly
US5315019A (en) * 1991-11-19 1994-05-24 Eastman Chemical Company Continuous process for the manufacture of 2,5-dihydrofurans from γ, δ-epoxybutenes
US5462075A (en) 1991-12-05 1995-10-31 Persson; Mats Method and device for controlling a flow of fluid
US5243996A (en) 1992-01-03 1993-09-14 Cook, Incorporated Small-diameter superelastic wire guide
WO1993013704A1 (en) 1992-01-09 1993-07-22 Endomedix Corporation Bi-directional miniscope
US5284128A (en) 1992-01-24 1994-02-08 Applied Medical Resources Corporation Surgical manipulator
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
DE69325692D1 (en) 1992-08-18 1999-08-26 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
DE69310754D1 (en) 1992-09-14 1997-06-19 Cytec Tech Corp Aqueous epoxygrundiermittelzusammensetzungen without volatile organic compounds
US5334145A (en) 1992-09-16 1994-08-02 Lundquist Ingemar H Torquable catheter
US5441483A (en) 1992-11-16 1995-08-15 Avitall; Boaz Catheter deflection control
ES2102187T3 (en) 1992-11-18 1997-07-16 Spectrascience Inc Apparatus for imaging diagnosis.
US5476701A (en) 1992-12-20 1995-12-19 Berger; David Table pad construction
US5341818A (en) 1992-12-22 1994-08-30 Advanced Cardiovascular Systems, Inc. Guidewire with superelastic distal portion
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
DE69432379D1 (en) 1993-01-26 2003-05-08 Terumo Corp Means for vascular dilation and catheter
EP0608775B1 (en) 1993-01-28 2001-03-21 ANGIOMED GmbH & Co. Medizintechnik KG One piece guidewire and process for the manufacture thereof
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
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 Micro Catheter.
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
DE69432359D1 (en) 1993-11-12 2003-04-30 Micro Interventional Systems P Catheter with a small diameter, 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
EP1229957B1 (en) 1999-11-16 2008-08-06 Abbott Cardiovascular Systems, Inc. Polymer coated guidewire
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
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
US5470387A (en) 1994-03-07 1995-11-28 Niro A/S Continuous multicell process and apparatus for particle coating including particle recirculation
JPH09504980A (en) * 1994-03-10 1997-05-20 シュナイダー・(ユーエスエイ)・インコーポレーテッド Catheter having a shaft of the variable stiffness
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
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
US5836923A (en) 1994-06-20 1998-11-17 Critical Device Corp. Needleless injection site with fixed flow rate
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
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
DE69527644T2 (en) 1994-11-23 2003-04-03 Micro Interventional Systems I A balloon catheter having a high torque
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
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
JPH0910315A (en) * 1995-06-30 1997-01-14 Ado Polymer:Kk Medical catheter
EP0755693A1 (en) 1995-07-18 1997-01-29 Schneider (Europe) Ag Catheter guide wire
US5702373A (en) * 1995-08-31 1997-12-30 Target Therapeutics, Inc. Composite super-elastic alloy braid reinforced catheter
US5746701A (en) 1995-09-14 1998-05-05 Medtronic, Inc. Guidewire with non-tapered tip
US6027461A (en) * 1995-10-11 2000-02-22 Micro Therapeutics, Inc. Infusion guidewire having fixed core wire and flexible radiopaque marker
US5997487A (en) 1995-10-11 1999-12-07 Micro Therapeutics, Inc. Infusion wire having fixed core wire
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
US5931830A (en) 1995-12-07 1999-08-03 Sarcos L.C. Hollow coil guide wire apparatus for catheters
EP0778039A1 (en) 1995-12-07 1997-06-11 Sarcos, Inc. Catheter guide wire
US20030069522A1 (en) 1995-12-07 2003-04-10 Jacobsen Stephen J. Slotted medical device
US5833632A (en) 1995-12-07 1998-11-10 Sarcos, Inc. Hollow guide wire apparatus catheters
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
JP3310849B2 (en) * 1996-01-18 2002-08-05 テルモ株式会社 Blood vessel dilator and catheter
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
JP3409270B2 (en) * 1996-03-26 2003-05-26 日本シャーウッド株式会社 Double lumen catheter
US5788653A (en) 1996-04-03 1998-08-04 Cordis Corporation Guidewire extension with sliding release mechanism
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
US5690120A (en) 1996-05-24 1997-11-25 Sarcos, Inc. Hybrid catheter guide wire apparatus
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
WO1997044086A1 (en) 1996-05-24 1997-11-27 Sarcos, Inc. Flexible balloon catheter/guide wire apparatus and method
US6440088B1 (en) 1996-05-24 2002-08-27 Precision Vascular Systems, Inc. Hybrid catheter guide wire apparatus and method
US5782811A (en) * 1996-05-30 1998-07-21 Target Therapeutics, Inc. Kink-resistant braided catheter with distal side holes
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
JP3165999B2 (en) * 1996-08-14 2001-05-14 東レ・メディカル株式会社 catheter
US6553880B2 (en) * 1996-09-16 2003-04-29 Sarcos, Lc Micromachining system
WO2001045912A1 (en) 1999-12-22 2001-06-28 Sarcos, Lc Method and apparatus for forming cuts in catheters, guidewires, and the like
US6014919A (en) 1996-09-16 2000-01-18 Precision Vascular Systems, Inc. Method and apparatus for forming cuts in catheters, guidewires, and the like
US5971975A (en) 1996-10-09 1999-10-26 Target Therapeutics, Inc. Guide catheter with enhanced guidewire tracking
JPH10118193A (en) 1996-10-21 1998-05-12 Tokin Corp Guide wire for catheter
US6001068A (en) 1996-10-22 1999-12-14 Terumo Kabushiki Kaisha Guide wire having tubular connector with helical slits
US5722614A (en) * 1996-10-30 1998-03-03 Mcdonnell Douglas Corporation Missile guidance command limitation system for dynamic controllability criteria
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
US6068623A (en) * 1997-03-06 2000-05-30 Percusurge, Inc. Hollow medical wires and methods of constructing same
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
US6042553A (en) * 1997-04-15 2000-03-28 Symbiosis Corporation Linear elastic member
US5895378A (en) 1997-05-29 1999-04-20 Target Therapeutics, Inc. Flow-directed catheter having multiple tapers and radio-opaque markers
WO1998055173A1 (en) * 1997-06-04 1998-12-10 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
US5947940A (en) 1997-06-23 1999-09-07 Beisel; Robert F. Catheter reinforced to prevent luminal collapse and tensile failure thereof
WO1999011313A1 (en) 1997-09-04 1999-03-11 Alcon Laboratories, Inc. Flexible tube with circular grooves of varying width and depth
US5980471A (en) 1997-10-10 1999-11-09 Advanced Cardiovascular System, Inc. Guidewire with tubular connector
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
US6022369A (en) * 1998-02-13 2000-02-08 Precision Vascular Systems, Inc. Wire device with detachable end
US6346091B1 (en) * 1998-02-13 2002-02-12 Stephen C. Jacobsen Detachable coil for aneurysm therapy
KR19990072499A (en) 1998-02-19 1999-09-27 리페르트 존 Catheter guidewire apparatus with location specific flexibility
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
JPH11342196A (en) * 1998-06-04 1999-12-14 Nippon Zeon Co Ltd Baloon catheter, and catheter auxiliary device
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
US6056702A (en) 1998-10-02 2000-05-02 Cordis Corporation Guidewire with outer sheath
US6059769A (en) * 1998-10-02 2000-05-09 Medtronic, Inc. Medical catheter with grooved soft distal segment
JP3645109B2 (en) 1998-10-27 2005-05-11 テルモ株式会社 Medical tubing and a 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
US6228073B1 (en) * 1998-12-15 2001-05-08 Medtronic, Inc. Angiography luer hub having wings proximal to the plurality of grips and strain relief
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
US6887235B2 (en) 1999-03-24 2005-05-03 Micrus Corporation Variable stiffness heating catheter
DE69917213T2 (en) 1999-03-29 2005-07-28 Cook Inc., Bloomington 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
WO2000066211A1 (en) 1999-04-30 2000-11-09 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
US6749560B1 (en) * 1999-10-26 2004-06-15 Circon Corporation Endoscope shaft with slotted tube
US6556873B1 (en) 1999-11-29 2003-04-29 Medtronic, Inc. Medical electrical lead having variable bending stiffness
US6352515B1 (en) * 1999-12-13 2002-03-05 Advanced Cardiovascular Systems, Inc. NiTi alloyed guidewires
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
DE60112078T2 (en) * 2000-05-17 2006-06-01 Cook Vascular Inc. An apparatus for removing cables from
US6530934B1 (en) 2000-06-06 2003-03-11 Sarcos Lc Embolic device composed of a linear sequence of miniature beads
US6428512B1 (en) 2000-10-10 2002-08-06 Advanced Cardiovascular Systems, Inc. Guidewire with improved lesion measurement
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 for an organic thin-film light emitting device and an organic thin film light emitting element
US6503244B2 (en) 2001-03-07 2003-01-07 Micro Therapeutics, Inc. High pressure injection 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
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
US6652508B2 (en) 2001-11-09 2003-11-25 Scimed Life Systems, Inc. Intravascular microcatheter having hypotube proximal shaft with transition
US6837898B2 (en) 2001-11-30 2005-01-04 Advanced Cardiovascular Systems, Inc. Intraluminal delivery system for an attachable treatment device
US6682493B2 (en) * 2001-12-03 2004-01-27 Scimed Life Systems, Inc. High torque guidewire
US6702762B2 (en) 2001-12-27 2004-03-09 Advanced Cardiovascular Systems, Inc. Apparatus and method for joining two guide wire core materials without a hypotube
US6730095B2 (en) 2002-06-26 2004-05-04 Scimed Life Systems, Inc. Retrograde plunger delivery system
DE60334122D1 (en) 2002-07-25 2010-10-21 Boston Scient Ltd A medical device for navigation through the anatomy
US6866642B2 (en) * 2002-11-25 2005-03-15 Advanced Cardiovascular Systems, Inc. Enhanced method for joining two core wires
US7771410B2 (en) 2002-11-25 2010-08-10 Invatec S.R.L. Pipe having at least a portion with a variable flexibility
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
US7001369B2 (en) * 2003-03-27 2006-02-21 Scimed Life Systems, Inc. Medical device
JP4213069B2 (en) 2003-09-02 2009-01-21 五洋建設株式会社 Marine seed plant growth material, manufacturing method and Construction method of marine seed plant growing field of marine seed plant growth material
JP4213070B2 (en) 2004-03-30 2009-01-21 川崎重工業株式会社 Railway for soundproofing
US20060264904A1 (en) 2005-05-09 2006-11-23 Kerby Walter L Medical device
JP5309519B2 (en) 2007-09-28 2013-10-09 凸版印刷株式会社 Image forming apparatus
DE102007055847A1 (en) 2007-12-18 2009-06-25 Zf Friedrichshafen Ag Servo-assistance device for motor vehicle change gear

Patent Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5238004A (en) 1990-04-10 1993-08-24 Boston Scientific Corporation High elongation linear elastic guidewire
EP0812599A2 (en) * 1991-05-07 1997-12-17 Target Therapeutics, Inc. Catheter guide wire
US5507766A (en) * 1993-01-26 1996-04-16 Terumo Kabushiki Kaisha Vascular dilatation instrument and catheter
US5772609A (en) 1993-05-11 1998-06-30 Target Therapeutics, Inc. Guidewire with variable flexibility due to polymeric coatings
US6139510A (en) 1994-05-11 2000-10-31 Target Therapeutics Inc. Super elastic alloy guidewire
US6428489B1 (en) 1995-12-07 2002-08-06 Precision Vascular Systems, Inc. Guidewire system
US6508803B1 (en) 1998-11-06 2003-01-21 Furukawa Techno Material Co., Ltd. Niti-type medical guide wire and method of producing the same
US20020013540A1 (en) 1999-12-22 2002-01-31 Jacobsen Stephen C. Coronary guidewire system
US20030009208A1 (en) * 2001-07-05 2003-01-09 Precision Vascular Systems, Inc. Torqueable soft tip medical device and method of usage

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2006122155A1 (en) * 2005-05-09 2006-11-16 Boston Scientific Limited Medical device
US9808595B2 (en) 2007-08-07 2017-11-07 Boston Scientific Scimed, Inc Microfabricated catheter with improved bonding structure

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US20040193140A1 (en) 2004-09-30 application
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US20170182291A1 (en) 2017-06-29 application
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US20090227983A1 (en) 2009-09-10 application
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