|Publication number||WO1993019803 A1|
|Publication date||14 Oct 1993|
|Filing date||29 Mar 1993|
|Priority date||31 Mar 1992|
|Also published as||DE69332950D1, DE69332950T2, DE69333513D1, DE69333513T2, DE69334302D1, EP0633798A1, EP0633798A4, EP0633798B1, EP0633799A1, EP0633799A4, EP0633799B1, EP1334701A2, EP1334701A3, EP1334701B1, US5725570, US6287331, US6290721, WO1993019804A1|
|Publication number||PCT/1993/2871, PCT/US/1993/002871, PCT/US/1993/02871, PCT/US/93/002871, PCT/US/93/02871, PCT/US1993/002871, PCT/US1993/02871, PCT/US1993002871, PCT/US199302871, PCT/US93/002871, PCT/US93/02871, PCT/US93002871, PCT/US9302871, WO 1993/019803 A1, WO 1993019803 A1, WO 1993019803A1, WO 9319803 A1, WO 9319803A1, WO-A1-1993019803, WO-A1-9319803, WO1993/019803A1, WO1993019803 A1, WO1993019803A1, WO9319803 A1, WO9319803A1|
|Inventors||Kevin R. Heath, John E. Abele|
|Applicant||Boston Scientific Corporation|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (2), Non-Patent Citations (1), Referenced by (65), Classifications (28), Legal Events (8)|
|External Links: Patentscope, Espacenet|
Field of the Invention This invention relates to metal medical components to be used inside the body, such as medical wires used, for example, in guidewires, filters, and other medical devices.
Background of the Invention Noninvasive medical procedures reduce the risk of surgery by introducing medical devices to a body cavity through small incisions or body orifices. The devices are carefully designed so that they may be controlled from the proxisaal end remaining outside the body to carry out the required treatment at the desired location inside the body. In one of the most common noninvasive techniques, angiography^ a device, such as a guidewire, balloon angioplasty catheter or the like, is advanced and to∑rqued at its proximal end to steer the device through a blood vessel to the position of an occlusion at which point a medical procedure such as balloon angioplasty and/or positioning of an endoprosthesis is carried out. Typically, X-ray fluoroscopy is used to view the medical device within the body cavity to monitor placement and operation. The device may also be viewed by X-ray film after placement. To use these techniques, particularly with small devices which may be difficult to view, the medical device must include some radiopaque material, more dense than the surrounding tissue, to provide sufficient contrast on an X-ray image. A highly dense, and therefore particularly radiopaque, metal is usually incorporated with the portion of the medical device used inside the body for this purpose.
Summary of the Invention In interventional medicine, wires can be used for a variety of purposes such as tracking, stenting. filtering, conducting (electric current, ultrasound energy, etc.) and marking. Desirable attributes of these wires vary with application, but include properties such as stiffness, tensile strength, elasticity, radiopacity, weldability, flexural life, conductivity, etc. These properties are hard to find in single-material constructions. It is possible to achieve optimum properties by creating a multiple material coaxial construction. In medical wires, for example, it can be very desirable to have high radiopacity along with elasticity and strength. This may be accomplished by combining a radiopaque material with an elastic material. Although it is possible to put either material on the inside or outside, it would be preferable to put the dense radiopaque material (e.g., tantalum) on the inside (core) since dense materials are generally less elastic and the elastic material (e.g., titanium or nickel- titanium alloy) on the outside (clad) . The clad or "skin" of the wire will undergo more deformation in bending than the core, so the elastic component is best positioned at the skin. In another medical application, it is desirable to have an elastic core (nitinol) for conducting axial vibrations (sonic or ultrasonic) and a thin stiff cladding (stainless steel) in order to minimize traverse vibrations which result in loss of energy.
An aspect of the invention is a metal medical device with at least a portion to be used within the body with properties that can be tailored to a particular application. The portion is formed of preferably two or more dissimilar metals joined together to form a unitary member. Typically, each metal contributes a desirable property to the device which is not substantially impaired by the presence of the other metal. In particularly preferred devices, one metal provides enhanced radiopacity. In these embodiments, the medical device comprises a metal outer member having a predetermined density and an exposed outer surface and a core including a metal having a density greater than the outer member to enhance radiopacity. The core is secured within and substantially enclosed by the outer member. Preferably, the medical component is in the form of a wire configured such that the mechanical properties, for example, the elastic properties, of the metal forming the outer member are affected by the core to a desired degree so that the wire has a desired overall performance suitable for its intended use. Preferably, the mechanical properties of the outer longitudinal member dominate the properties of the wire yet the radiopacity is substantially enhanced by the ťanser core. The invention also allows increased radiopacity of a metal medical device wit__.o_r_. adversely affecting and in some cases improving other important properties such as the biocompatibility, size or other performance characteristics. These performance advantages can pe realized by proper selection of the material of the outer member and core, their relative size, and geometrical configuration. The performance characteristics of the component may be dictated by the medical device into which the radiopaque medical component is to be incorporated.
The term "metal" as used herein includes electropositive chemical elements characterized by ductility, malleability, luster, and conductivity of heat and electricity, which can replace the hydrogen of an acid and forms bases with the hydroxyl radical and including mixtures including these elements and alloys. Many examples are given below.
In one aspect, the invention features a medical device having at least a portion for use within the body. The portion includes an extended metal outer member having an exposed outer surface and a core within the outer member formed of a metal dif erent than the metal of the outer member. The core is secured within and substantially enclosed by the outer member.
Various preferred embodiments may include one or more of the following features. The extended metal outer member is comprised of a metal of predetermined density and the core is comprised of a metal having a density substantially greater than the outer member to enhance radiopacity of the device. The portion is in the form of a medical wire, wherein the metal outer member is a longitudinal member and the radiopaque core is positioned along the axis of the longitudinal member. The radiopaque core has a density of about 9.9 g/cc or greater. The core is selected from the group consisting of tungsten, tantalum, rhenium, iridium, silver, gold, bismuth, platinum and alloys thereof. The core has a modulus of elasticity of about 550 GPa or less. The core has a modulus of elasticity of about 200 GPa or less.
The outer member is selected from the group consisting of superelastic alloys, precursor alloys of superelastic alloys, stainless steel, and titanium and its alloys.
The superelastical alloy is nitinol. The core is about 1 to 40% of the cross-sectional dimension of the component. The core is about 25% or more of the cross- sectional dimension of the component. The core is about 28% or less of the cross-sectional dimension of the component. The cross-sectional dimension of the component is less than about 0.025 inch. The outer member has a cross-section of about 0.0045 to 0.008 inch and the core member has a cross-section of about 0.0014 to 0.00195 inch inner diameter. The core is a solid metallic member. The outer member has portions of varying dimension. The outer member has a taper portion. The core has a constant inner dimension in portions corresponding to the varying outer dimension of the outer member. The portion is in the form of a medical guidewire. The portion is in the form of elastic leg members of a vascular filter. The outer member and core are of circular cross-sectional configuration. The portion is in the form of an ultrasonic probe. The probe is an elastic probe having a titanium core and nitinol outer member. The probe and core are constructed of materials of substantially different acoustic impedance. The acoustic energy is provided by axial excitation.
In another aspect, the invention features a medical wire device having at least a portion for use within the body. The portion includes an extended longitudinal metal outer member having a predetermined density and an exposed outer surface and a continuous solid core positioned along the axis of the outer member including a metal having a density of about 9.9 g/cc or greater and greater than the density of the outer member for enhancing radiopacity of the wire. The core is secured within and substantially enclosed by the outer member and is about 10 to 50% of the cross-sectional dimension of the portion for use within the body. In various preferred embodiments, the core material is tantalum, the outer material is nitinol, and the cross sectional dimension of the portion is about 0.025 inch or less. The outer member has a cross-section of about 0.0045 to 0.008 inch and the core member has a cross-section of about 0.0014 to 0.00195 inch inner diameter. The wire is in the form of a guidewire. The outer member has portions of varying dimension such as a taper portion. The core has a constant inner dimension in portions corresponding to the varying outer dimension of the outer member. The cross-sectional dimension of the portion is about 0.035 to 0.037 inch. The core is about 0.005 inch in diameter. The component is in the form of elastic leg members of a vascular filter.
In another aspect, the invention features a method or medical treatment by providing a medical device for performing a desired treatment, incorporating on at least a portion of the device a radiopaque medical component, formed of a metal outer member having a predetermined density and exposed outer surface and a core including a metal having a density substantially greater than the outer member to enhance radiopacity, the core being secured within and substantially enclosed by the outer member, and introducing the portion including the radiopaque medical component into the body, and observing the medical component by x-ray fluoroscopy. In various preferred embodiments, the medical device is a guidewire and the medical component is a portion of the guidewire, the method further including steering the guidewire through the body from the proximal end. The medical device is a vascular filter. In another aspect, the invention features a medical device capable of placement or manipulation in the body by means external of the body under guidance of a fluoroscope. The device is formed at least in part of an elongated wire-form metal member adapted to be subjected to elastic deformation to enable the device to be forced into a characteristic deformed configuration during a stage of use and to elastically self-recover from the deformation when deformation forces are relieved. The wire-form metal member is formed of a core of a first metal of a first selected thickness and an intimately surrounding sheath of a second selected metal of a second thickness, the first metal being a high density metal that demonstrates characteristic relatively high radiopacity and the second metal being a lower density metal having substantially more elasticity than the first metal, the combined effect of the selected thicknesses of the first and second metals in the wire- form member serving to enhance the radio-opacity of the wire-form member to provide improved fluoroscopic or x- ray visualization of the wire-form member in the body while imparting sufficient elasticity to enable the wire- form member to elastically self-recover from its characteristic deformed configuration.
In various preferred embodiments, the wire-form metal member comprises a draw-form. The second metal is nitinol. The high density metal is tantalum. The wire- form member comprises the main body of a medical guidewire.
Description of the Preferred Embodiment (s) We first briefly describe the drawings. Drawings
Fig. 1 is a longitudinal cross-sectional view of a medical wire according to the invention; while Fig. la is a cross-sectional view taken along the lines aa in Fig. 1;
Fig. 2 is a schematic illustration of a wire according to the invention in a stressed, bent configuration;
Fig. 3 is a graph of load versus displacement for several wires according to the invention;
Fig. 4 is a view of a guidewire of the invention for introduction into a body lumen; while Fig. 4a a cross-sectional view along lines bb, Fig. 4b is a cross- sectional view along lines cc in Fig. 4; and Fig. 4c is a greatly enlarged cross-sectional view of portion d of Fig. 4;
Fig. 5 is a schematic of a blood clot filtration device of the invention for implantation in a blood vessel; Fig. 6 is a schematic illustration of an ultrasonic wire device of the invention and Fig. 6a is longitudinal cross-sectional view of a portion of another embodiment of an ultrasonic device, having air-filled microspheres (shown greatly enlarged) at the interface of the core and outer member. Description
Referring to Figs. 1 and la, a preferred embodiment of the invention is a medical wire 2 that includes a longitudinal outer member 4 with an axis 6. The longitudinal member 4 is formed of a metal having desirable properties, such as high elasticity and biocompatibility of its exposed outer surface 7. (The surface 7 may include a non-metal coating of, e.g., fluorocarbons, silicones, hydrophilic and lubricous biocompatible materials.) About the axis 6 is a core material 8 including a metal with a density greater than the longitudinal member 4 to enhance the radiopacity of the wire. The core 8 is bonded to and substantially enclosed by the outer member 4 such that it does not have any substantial exposed surface and therefore does not contact body tissue when positioned within the body during use.
As illustrated, preferably the core 8 is a continuous solid member in intimate contact and bonded with the outer member 4 without the formation of substantial voids in the interface 10 between the core and outer member. Preferably, the elastic properties of the wire 2 are dominated by the elastic properties of the longitudinal member 4. The core material 8 enhances the radiopacity of the wire 2 but preferably does not substantially effect the mechanical performance of the wire. In preferred embodiments, the cross-sectional dimension of the core (dc) is less than about 70% (but typically greater than about 1% or 10%) of the outer cross-sectional dimension (d0) of the wire, more preferably between about 40% and 25%. The wire is especially useful in applications where the medical device must be sized small, such as for use in the vascular system, for example, as a guidewire tip which has an outer dimension (d0) of less than about 0.015 inch, e.g., even less than 0.0075 inch and for which less dense metals are required for advantageous elastic properties. The invention is particularly useful for enhancing radiopacity of devices with dimensions of about 0.025 inch or less.
Referring to Fig. 2, the wire 2 is shown in a bent position, as it may be, for example when in use in a device positioned within the body. The inner and outer portions (i) and (o) , experience a wide range of tension and compression as the wire is bent. An advantage of the invention, is that by positioning the core material 8 near the axis 6, the range of tension and compression imposed on the core is reduced and a wide latitude of dense, substantially radiopaque materials can be used which would otherwise might not be suitable for their response to bending or other mechanical properties. The relative dimension of the core and outer member and the particular materials used for these elements are selected based on the desired over-all mechanical properties of the wire and the degree to which x-ray visibility is to be enhanced, since the core affects the mechanical properties of the wire compared to a solid wire formed of the outer material, and the radiopacity is a function of the sum of the mass between an x-ray beam source and detector. For example, large devices or devices with overlapping portions, may require less radiopaque material to provide sufficient visibility. Similarly, the location of use in the body may affect the amount of dense material needed for sufficient visibility. The visibility of a device can be tested by known techniques such as ASTM Designation F640- 79 "Standard Test Method for Radiopacity of Plastics for Medical Use". In this test, the background densities which may be encountered clinically are mimicked by an aluminum plate positioned over the wire having various thicknesses.
The properties of the outer member metal and core which may be considered include density, modulus of elasticity (in annealed and hardened states) , biocompatability (primarily a factor for the material of the outer longitudinal member) , flexural stiffness, durability, tensile and compression strength, acoustic impedance (as discussed in a further embodiment below) and the required radiopacity and resolution.
Preferably, for elastic members, the outer member is formed of a continuous solid mass of a highly elastic biocompatible metal such as a superelastic or pseudo- elastic metal alloy, for example, a nitinol (e.g., 55% nickel, 45% titanium) . Other examples of superelastic materials include, e.g., Silver-Cadmium (Ag-Cd) , Gold- Cadmium (Au-Cd) , Gold-Copper-Zinc (Au-Cu-Zn) , Copper- Aluminum-Nickel (Cu-Al-Ni) , Copper-Gold-Zinc (Cu-Au-Zn) , Copper-Zinc (Cu-Zn) , Copper-Zinc-aluminum (Cu-Zn-Al) , Copper-Zinc-Tin (Cu-Zn-Sn) , Copper-Zinc-Xenon (Cu-Zn-Xe) , Iron Beryllium (Fe3Be) , Iron Platinum (Fe3Pt) , Indium- Thallium (In-Tl) , iron-manganese (Fe-Mn) Nickel-Titanium- Vanadium (Ni-Ti-V) , Iron-Nickel-Titanium-Cobalt (Fe-Ni- Ti-Co) and Copper-Tin (Cu-Sn) . See Schetsky, L. McDonald, "Shape Memory Alloys" , Encyclopedia of Chemical Technology (3rd ed.), John Wiley & Sons, 1982, vol. 20. pp. 726-736 for a full discussion of superelastic alloys. Other examples of metals suitable for the outer member include stainless steel, titanium and various alloys of these metals and the precursor of superelastic alloys. Precursors of superelastic alloys are those alloys which have the same chemical constituents as superelastic alloys, but have not been processed to impart the superelastic property. Such alloys are further described in co-owned and co-pending U.S. Serial No. 07/507,375, filed April 10, 1990, the entire contents of which is hereby incorporated by reference.
The core material is preferably a continuous solid mass, but may also be in a powder-form. The core includes a metal that is relatively dense to enhance radiopacity. Preferably, the core metal has a density of about 9.9 g/cc or greater. Most preferably, the core is formed of tantalum (density = 16.6 g/cc). Other preferred materials and their density include tungsten (19.3 g/cc), rhenium (21.2 g/cc), bismuth (9.9 g/cc), silver (16.49 g/cc), gold (19.3 g/cc), platinum (21.45 g/cc), and iridium (22.4 g/cc). In some cases barium can be used in the core. The core may be formed of alloys such as those including the above materials. Typically, the core is somewhat stiffer than the outer membrane. Preferably, the core metal has a low modulus of elasticity, e.g., preferably below about 550 GPa, e.g., such as tantalum (186 GPa) . A smaller difference between the modulus of elasticity between the outer material and core, results in a smaller variation of the modulus from that of the outer material in the wire of the invention. For larger differences, a smaller core may be used so as to produce a wire in which the elastic properties are dominated by the outer material. The outer member and core may be in many cross- sectional geometric configurations, such as circular, square, triangular, hexagonal, octagonal, trapezoidal and the geometrical configuration of the core may differ from that of the longitudinal member. For example, the wire may be rectangular in cross-section with a rectangular core or triangular or hexagonal in cross-section with a circular core. The wire may also take on the form of tubing with a lumen within the core extending along the axis of the wire. The wire may also include successive layers of different metals to form a composite system. The core may extend intermittently along the axis in a desired pattern.
The medical device may be formed, for example, by drilling a relatively large rod of the outer member material to form a lumen, positioning a rod of core material in the lumen, sealing the ends of the lumen, e.g. , by crimping and drawing as known in the art, through a series of dies of decreasing diameter until the desired outer diameter is achieved. The device may be heat treated to anneal, harden or impart superelastic properties. Other methods of formation may be, e.g., by coating the core with the desired outer material such as by electro- or eleσtroless plating. The materials used in the outer member and core are also selected based on their workability for forming the wire, including factors such as machinability, for forming the longitudinal member into a tubular piece and the core member into a rod shaped piece, stability in gaseous environments at annealing temperatures, properties related to welding, drawing, forging, swaging, the ability to accept coatings such as adhesives, polymers, lubricants and practical aspects such as cost and availability. Other examples follow. Example 1 A 500 foot length of wire (0.0052 inch in diameter) having an outer member formed of a precursor of a nitinol (55% Ni/45% Ti) superelastic alloy and a core material of tantalum (0.00175 inch in diameter) is formed by drilling a 0.25 inch diameter bore in a 0.75 inch rod of the outer member material and providing in the drilled lumen a tantalum member of substantially matched outer diameter. The rod is mechanically forged in a standard hot forging and rolling apparatus, then hammered such that no substantial voids between the core and outer longitudinal member are present. One end of the rod is sealed and the opposite end is cold drawn longitudinally through a dye to the final diameter. Initially, the outer member of the wire is the precursor of a superelastic alloy, i.e., it has not been heat treated to impart the superelastic property.
Referring to Fig. 3, load versus displacement curves are illustrated. (For clarity, curves C, D and A are offset, successively, 0.025 inch on the x-axis.) Curve A illustrates the wire as discussed in the above paragraph prior to heat annealing which induces the superelastic property; the wire exhibits substantially linear elastic strain as a function of stress to a break point z. Curves B, C, D illustrate stress/strain curves after annealing the wire at 460°C for 3 minutes, 5 minutes and 15 minutes, respectively. As these curves illustrate, the superelastic nature of the wire is substantially preserved, as evidenced by the substantial plateaus (p) on the stress/strain curve, despite the presence of the tantalum core. Also as illustrated, the stress at which constant displacement occurs decreases with increasing annealing, as would be expected with a superelastic material. The mechanical properties of the wire, therefore, are dominated by the nitinol alloy, despite the presence of the tantalum core.
Referring to Table I, the modulus of elasticity and plateau stress calculated based on stress-strain measurements as above, are compared for the wires of the invention and a solid wire of Ni-Ti alloy.
X Charge in Cored Wire
As the results in Table I illustrate, the modulus of elasticity of the wires of the invention was varied less than 30% compared to the solid Ni-Ti wire. The plateau stress of the wires of the invention using a superelastic outer member was varied less than about 10% compared to a solid Ni-Ti superelastic wire. The wire formed as described exhibits about 30% or more enhanced x-ray visibility over a wire of the same thickness formed of solid material. Preferably, wires as described, dominated by the mechanical properties of the outer superelastic member and exhibiting generally satisfactory radiopacity have outer diameter (d0) of about 0.008 to 0.0045 inch with a core diameter (dc) of about 0.0014 to 0.00195 inch. Example 2 Referring now to Fig. 4, a guidewire is shown of the type introduced into the body lumen, e.g., a blood vessel for positioning, for example, a catheter or the like. The guidewire 60 includes a proximal body section 62 of constant diameter, a taper 64 and a distal end 66 of constant, smaller diameter than the body section 62. Referring to Fig. 4a, in the preferred embodiment, the outer diameter of the proximal end 62 is d_0 about 0.038 inch and the diameter of the core is, c c, about 0.003 inch. Referring to Fig. 4b, at the distal end 66, the outer diameter is ddo about 0.005 to 0.008 inch and the core is ddc about 0.003 inch. In the taper 64, only the outer member 4 tapers to reduced diameter, while the core remains of constant diameter. Such a wire might be formed by preparing a specimen of the outer material with an inner lumen, drawing the outer material to form the taper and reduced diameter distal portion, followed by positioning the core in the lumen. Alternatively, the structure of Figs. 4 et seg. could be formed from a, wire of constant diameter outer member and core and removing portions of the outer member, e.g., by grinding, to leave a relatively lower ratio of outer member to core in the taper and distal end. Alternatively, the core may taper at the same position as the outer member tapers by drawing the wire to form the taper after positioning the core within the outer material. The radiopaque core preferably extends the length of the wire so that the entire wire can be imaged, allowing viewing of the length of a tortuous body lumen. The cored wire may also be used as the distal tip of a conventional wire. The guidewire may also include a coil spring, e.g., about the distal tapered region, and/or incorporate a polymer coating. As well as improving the radiopacity, the cored wire can be tailored to exhibit other advantageous features, such as enhanced tensile strength by using a core material that has this property.
Example 3 Referring to Fig. 5, a wire of the invention may also be used in a blood clot filtration device of the type positioned within a blood vessel. The filtration device 50 includes a nose cone 52 downstream relative to blood flow 58 and a series of legs 54. The legs include hook members 102 which are embedded in the wall 56 of the body lumen to secure the filter therein. A filter of this type is further described in Herms U.S. 4,817,600 and El-Nou Nou U.S. 5,059,205, the entire contents of which are hereby incorporated by reference. The wires 54 are formed as described herein including a radiopaque core within an elastic longitudinal member. Preferably, the overall diameter of the wire is 0.035 to 0.037 with a core diameter of about 0.005 inch. The outer member is preferably nitinol, stainless steel or titanium and the core is tantalum. It will be understood that smaller diameter wires for smaller filtration device legs may also be used, in which case, a dense core is particularly useful for enhancing radiopacity.
Example 4 Referring now to Figs. 6 and 6a, an ultrasonic device 70 is shown to include a wire 72 including an inner core 74 and an outer member 76. The wire 72 extends from a proximal end 78, attached to an ultrasonic source mechanism 80, to a distal end 82 which is positioned at a location where ultrasonic energy is to be delivered. Briefly, the source 80 includes a clamping mechanism 86 to couple the core near the distal end 78 of the wire to a diaphragm 88 which is vibrated ultrasonically by a piston transducer 90. The transducer 90 includes a phosphorous-bronze bell 92 whose tension may be adjusted by screw member 94. The magnetic field from coils 96 cause the transducer to vibrate when electrical energy is supplied through leads 98. Cooling vents 100 surround the coils 98. Ultrasonic energy supplied by the mechanism 80 to the core at the proximal portion 78 of the wire is transmitted through the core to the distal end 82 where it can be utilized to treat tissue. Referring to Fig. 6a, in some embodiments, the core 74 is bonded to the outer member 76 at intermittent points, leaving therebetween air-filled microspheres 102 which impede the transmission of ultrasonic energy laterally. The microspheres could be produced by machining grooves into the core or outer member before assembly.
By proper selection of the outer and core metals enhanced transmission of ultrasonic energy through the core may be achieved while minimizing lateral mode losses through the outer material. Preferably, the metals are selected based on their acoustic impedance (Z , Z2) to induce internal reflection of acoustic waves propagating off axis. An advantage of the system is that lower power may be applied so that the transmission system operates at lower temperature. The outer member can further be selected to reduce vibration. A preferred embodiment of an elastic probe employs high acoustic transmitting titanium at the core and nitinol as the outer member. In another embodiment, the core member may be for example, nitinol and the outer member stainless steel. In another embodiment, the core is tantalum. The outer member could also be formed of a non-metal, e.g., carbon or glass. The ultrasound energy could be used to ablate tissue, enhance delivery of drugs and induce relaxation of tissue, e.g., tumors and in eye surgery e.g., to dissolve cataracts. The acoustic energy can be provided to the probe by axial excitation as illustrated above or by torsional excitation or a combination thereof. Other Examples _
The invention can be embodied in examples too numerous to mention, as will be understood by those skilled in the art. While the preferred embodiment described herein is in the form of a wire, it will be realized that medical components could be of various shapes and configurations including e.g., a radiopaque core and less dense outer member. In other embodiments, the outer member is substantially more radiopaque (e.g., tantalum) compared to the inner member (e.g., stainless steel) , for example, for use in guidewire applications to provide a highly radiopaque wire with enhanced flexibility.
Other embodiments are in the following claims.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US4950227 *||7 Nov 1988||21 Aug 1990||Boston Scientific Corporation||Stent delivery system|
|US5069226 *||27 Apr 1990||3 Dec 1991||Tokin Corporation||Catheter guidewire with pseudo elastic shape memory alloy|
|1||*||See also references of EP0633798A4|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|WO1996008208A1 *||12 Sep 1995||21 Mar 1996||Biopsys Medical, Inc.||Methods and devices for defining and marking tissue|
|WO1996017634A2||28 Nov 1995||13 Jun 1996||Boston Scientific Corporation||Blood clot filtering|
|WO2000061203A1 *||13 Apr 2000||19 Oct 2000||Elephant Dental B.V.||Biomedical aid or implant|
|WO2001034041A1 *||26 Oct 2000||17 May 2001||Boston Scientific Limited||Retrieval device made of precursor alloy cable|
|WO2003082362A3 *||18 Mar 2003||15 Jan 2004||Scimed Life Systems Inc||Mri and x-ray compatible stent material|
|WO2004093742A1 *||10 Mar 2004||4 Nov 2004||Boston Scientific Limited||Embolic filter loop fabricated from composite material|
|WO2005025454A2 *||9 Sep 2004||24 Mar 2005||Boston Scientific Limited||Composite medical devices|
|WO2005025454A3 *||9 Sep 2004||5 Jan 2006||Boston Scient Ltd||Composite medical devices|
|WO2006053270A2||10 Nov 2005||18 May 2006||Boston Scientific Limited||Atraumatic stent with reduced deployment force, method for making the same and method and apparatus for deploying and positioning the stent|
|WO2006053270A3 *||10 Nov 2005||24 Aug 2006||Boston Scient Scimed Inc||Atraumatic stent with reduced deployment force, method for making the same and method and apparatus for deploying and positioning the stent|
|WO2006124541A3 *||11 May 2006||5 Mar 2009||Boston Scient Ltd||Integrated stent repositioning and retrieval loop|
|DE10301850B4 *||16 Jan 2003||4 May 2017||Dendron Gmbh||Stent|
|EP0809998A2 *||27 May 1997||3 Dec 1997||Cordis Corporation||Composite material endoprosthesis|
|EP0809998A3 *||27 May 1997||17 Nov 1999||Cordis Corporation||Composite material endoprosthesis|
|EP0947204A2 *||29 Mar 1999||6 Oct 1999||Cordis Corporation||Composite material endoprosthesis|
|EP0947204A3 *||29 Mar 1999||20 Dec 2000||Cordis Corporation||Composite material endoprosthesis|
|EP2407127A1 *||10 Nov 2005||18 Jan 2012||Boston Scientific Scimed, Inc.||Atraumatic stent with reduced deployment force|
|EP2666508A1 *||11 May 2006||27 Nov 2013||Boston Scientific Limited||Integrated stent repositioning and retrieval loop|
|US5628787 *||7 Jun 1995||13 May 1997||Schneider (Usa) Inc.||Clad composite stent|
|US5733326 *||28 May 1996||31 Mar 1998||Cordis Corporation||Composite material endoprosthesis|
|US5824077 *||6 Jun 1995||20 Oct 1998||Schneider (Usa) Inc||Clad composite stent|
|US5888201 *||13 Jun 1997||30 Mar 1999||Schneider (Usa) Inc||Titanium alloy self-expanding stent|
|US5902310 *||21 Feb 1997||11 May 1999||Ethicon Endo-Surgery, Inc.||Apparatus and method for marking tissue|
|US6027528 *||30 Mar 1998||22 Feb 2000||Cordis Corporation||Composite material endoprosthesis|
|US6228055||19 May 1997||8 May 2001||Ethicon Endo-Surgery, Inc.||Devices for marking and defining particular locations in body tissue|
|US6402761||8 Mar 2001||11 Jun 2002||Scimed Life Systems, Inc.||Retrieval device made of precursor alloy cable|
|US7087077||13 Apr 2000||8 Aug 2006||Elephant Dental Bv||Biomedical aid or implant|
|US7208172||3 Nov 2003||24 Apr 2007||Medlogics Device Corporation||Metallic composite coating for delivery of therapeutic agents from the surface of implantable devices|
|US7452501||18 Nov 2005||18 Nov 2008||Icon Medical Corp.||Metal alloy for a stent|
|US7452502||18 Nov 2005||18 Nov 2008||Icon Medical Corp.||Metal alloy for a stent|
|US7462192||10 Nov 2005||9 Dec 2008||Boston Scientific Scimed, Inc.||Atraumatic stent with reduced deployment force, method for making the same and method and apparatus for deploying and positioning the stent|
|US7540994||30 Jan 2006||2 Jun 2009||Icon Medical Corp.||Process for forming an improved metal alloy stent|
|US7540995||1 Dec 2006||2 Jun 2009||Icon Medical Corp.||Process for forming an improved metal alloy stent|
|US7604662||13 Jul 2007||20 Oct 2009||Boston Scientific Scimed, Inc.||Endoprostheses containing boride intermetallic phases|
|US7648590||17 Nov 2008||19 Jan 2010||ICON International Systems, Inc.||Metal alloy for a stent|
|US7648591||17 Nov 2008||19 Jan 2010||Icon Medical Corp.||Metal alloys for medical devices|
|US7648592||17 Nov 2008||19 Jan 2010||Icon Medical Corp.||Metal alloy for a stent|
|US7670355||14 Nov 2007||2 Mar 2010||Ev3 Inc.||Method and device for filtering body fluid|
|US7670356||14 Nov 2007||2 Mar 2010||Ev3 Inc.||Method and device for filtering body fluid|
|US7678130||6 Dec 2004||16 Mar 2010||Ev3 Inc.||Method and device for filtering body fluid|
|US7686815||3 May 2005||30 Mar 2010||Ev3 Inc.||Method and device for filtering body fluid|
|US7776379||12 Aug 2005||17 Aug 2010||Medlogics Device Corporation||Metallic structures incorporating bioactive materials and methods for creating the same|
|US7828815||3 May 2005||9 Nov 2010||Ev3 Inc.||Method and device for filtering body fluid|
|US7828816||14 Nov 2007||9 Nov 2010||Ev3 Inc.||Method and device for filtering body fluid|
|US7857844||30 Oct 2008||28 Dec 2010||Boston Scientific Scimed Inc.|
|US7922732||14 Nov 2007||12 Apr 2011||Tyco Healthcare Group Lp||Method and device for filtering body fluid|
|US7947060||14 Nov 2007||24 May 2011||Tyco Healthcare Group Lp||Method and device for filtering body fluid|
|US8128579||2 Nov 2007||6 Mar 2012||Boston Scientific Scimed, Inc.||Guidewires with improved fatigue life and methods of making the same|
|US8221434||3 Aug 2010||17 Jul 2012||Boston Scientific Scimed, Inc.||Retrieval device made of precursor alloy cable|
|US8398702||29 Jun 2007||19 Mar 2013||Boston Scientific Scimed, Inc.||Molybdenum endoprostheses|
|US8398916||4 Mar 2010||19 Mar 2013||Icon Medical Corp.||Method for forming a tubular medical device|
|US8956389||7 Jul 2009||17 Feb 2015||W. L. Gore & Associates, Inc.||Sealing device and delivery system|
|US9034245||25 Feb 2013||19 May 2015||Icon Medical Corp.||Method for forming a tubular medical device|
|US9107899||5 Oct 2012||18 Aug 2015||Icon Medical Corporation||Metal alloys for medical devices|
|US9265634||11 May 2006||23 Feb 2016||Boston Scientific Scimed, Inc.||Integrated stent repositioning and retrieval loop|
|US9380998||20 Feb 2014||5 Jul 2016||Devicor Medical Products, Inc.||Subcutaneous cavity marking device and method|
|US9381006||8 Nov 2011||5 Jul 2016||W. L. Gore & Associates, Inc.||Sealing device and delivery system|
|US9451939||14 Mar 2013||27 Sep 2016||W. L. Gore & Associates, Inc.||Sealing device and delivery system|
|US9468430||12 Feb 2015||18 Oct 2016||W. L. Gore & Associates, Inc.||Sealing device and delivery system|
|US9474517||31 Mar 2016||25 Oct 2016||W. L. Gore & Associates, Inc.||Heart occlusion devices|
|US9492570||11 May 2010||15 Nov 2016||Devicor Medical Products, Inc.||Device and method for safe location and marking of a biopsy cavity|
|US9636094||7 Jul 2009||2 May 2017||W. L. Gore & Associates, Inc.||Sealing device and delivery system|
|US9669113||23 Dec 1999||6 Jun 2017||Devicor Medical Products, Inc.||Device and method for safe location and marking of a biopsy cavity|
|US9770232||9 Aug 2012||26 Sep 2017||W. L. Gore & Associates, Inc.||Heart occlusion devices|
|US9808230||4 Jun 2015||7 Nov 2017||W. L. Gore & Associates, Inc.||Sealing device and delivery system|
|International Classification||A61F2/90, A61L31/02, A61L31/08, A61M25/01, A61B19/00, A61F2/00, A61L31/18, A61F2/01|
|Cooperative Classification||A61B90/39, A61F2230/0006, A61F2/90, A61F2/01, A61L31/022, A61F2250/0098, A61F2240/001, A61M2025/09166, A61M25/0108, A61L31/18, A61F2210/0019, A61L31/088, A61F2230/0013|
|European Classification||A61B19/54, A61L31/18, A61L31/02B, A61F2/01, A61M25/01C1, A61L31/08B6, A61F2/90|
|14 Oct 1993||AK||Designated states|
Kind code of ref document: A1
Designated state(s): CA JP
|14 Oct 1993||AL||Designated countries for regional patents|
Kind code of ref document: A1
Designated state(s): AT BE CH DE DK ES FR GB GR IE IT LU MC NL PT SE
|6 Jan 1994||DFPE||Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101)|
|12 Jan 1994||121||Ep: the epo has been informed by wipo that ep was designated in this application|
|6 Oct 1994||WWE||Wipo information: entry into national phase|
Ref document number: 1993908616
Country of ref document: EP
|18 Jan 1995||WWP||Wipo information: published in national office|
Ref document number: 1993908616
Country of ref document: EP
|30 Nov 1995||NENP||Non-entry into the national phase in:|
Ref country code: CA
|7 May 2003||WWG||Wipo information: grant in national office|
Ref document number: 1993908616
Country of ref document: EP