WO1995030384A2 - Extenseur composite plaque - Google Patents

Extenseur composite plaque Download PDF

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Publication number
WO1995030384A2
WO1995030384A2 PCT/IB1995/000253 IB9500253W WO9530384A2 WO 1995030384 A2 WO1995030384 A2 WO 1995030384A2 IB 9500253 W IB9500253 W IB 9500253W WO 9530384 A2 WO9530384 A2 WO 9530384A2
Authority
WO
WIPO (PCT)
Prior art keywords
core
case
weight percent
elongate
filaments
Prior art date
Application number
PCT/IB1995/000253
Other languages
English (en)
Other versions
WO1995030384A3 (fr
Inventor
David W. Mayer
Original Assignee
Schneider (Usa) Inc.
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
Application filed by Schneider (Usa) Inc. filed Critical Schneider (Usa) Inc.
Priority to CA002188429A priority Critical patent/CA2188429C/fr
Priority to JP52880295A priority patent/JP3415158B2/ja
Priority to MX9605485A priority patent/MX9605485A/es
Priority to EP95913307A priority patent/EP0758870A1/fr
Publication of WO1995030384A2 publication Critical patent/WO1995030384A2/fr
Publication of WO1995030384A3 publication Critical patent/WO1995030384A3/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS 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
    • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/02—Inorganic materials
    • A61L31/022—Metals or alloys
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS 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
    • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/08—Materials for coatings
    • A61L31/082—Inorganic materials
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS 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
    • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L31/18—Materials at least partially X-ray or laser opaque
    • D—TEXTILES; PAPER
    • D04—BRAIDING; LACE-MAKING; KNITTING; TRIMMINGS; NON-WOVEN FABRICS
    • D04C—BRAIDING OR MANUFACTURE OF LACE, INCLUDING BOBBIN-NET OR CARBONISED LACE; BRAIDING MACHINES; BRAID; LACE
    • D04C1/00—Braid or lace, e.g. pillow-lace; Processes for the manufacture thereof
    • D04C1/06—Braid or lace serving particular purposes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0076—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof multilayered, e.g. laminated structures
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0008—Fixation appliances for connecting prostheses to the body
    • A61F2220/0016—Fixation appliances for connecting prostheses to the body with sharp anchoring protrusions, e.g. barbs, pins, spikes

Definitions

  • the present invention relates to body implantable medical devices, and more particularly to stents and other prostheses configured for high radio-opacity as well as favorable mechanical characteristics.
  • prostheses typically of lattice work or open frame construction
  • intravascular stents for treating stenosis
  • prostheses for maintaining openings in the urinary tracts
  • biliary prostheses e.g. esophageal stents
  • renal stents e.g. vena cava filters to counter thrombosis.
  • One particularly well accepted device is a self-expanding mesh stent disclosed in U. S. Patent No. 4,655,771 (Wallsten).
  • the stent is a flexible tubular braided structure formed of helically wound thread elements.
  • the thread elements can be constructed of a biocompatible plastic or metal, e.g. certain stainless steels, polypropylene, polyesters and polyurethanes.
  • stents and other prostheses can be expandable by plastic deformation, usually by expanding a dilation balloon surrounded by the prosthesis.
  • U. S. Patent No. 4,733,665 discloses an intraluminal graft constructed of stainless steel strands, either woven or welded at their intersections with silver.
  • U. S. Patent No. 4,886,062 (Wiktor) features a balloon expandable stent constructed of stainless steel, a copper alloy, titanium, or gold.
  • the stent itself must be radiopaque.
  • the Wolff patent suggests that the stent can be formed of platinum or a platinum-iridium alloy for substantially greater radio-opacity. Such stent, however, lacks the required elasticity, and would exhibit poor resistance to fatigue.
  • the Wiktor '110 patent teaches the attachment of metal staples to its blood vessel liner, to enhance radio-opacity. However, for many applications (e.g. in blood vessels), the stent is so small that such staples either would be too small to provide useful fluoroscopic imaging, or would adversely affect the efficiency and safety of deploying the stent or other prosthesis.
  • This Wiktor patent also suggests infusing its plastic strands with a suitable filler, e.g.
  • Wiktor provides no teaching as to how this might be done. Further, given the small size of prostheses intended for blood vessel placement, this technique is unlikely to materially enhance radio-opacity, due to an insufficient amount and density of the gold or barium sulfate.
  • Another object is to provide a resilient body insertable composite filament having a high degree of radio-opacity and favorable structural characteristics, even for stents employing relatively small diameter filaments.
  • a further object is to provide a process for manufacturing a composite filament consisting essentially of a structural material for imparting desired mechanical characteristics, in combination with a radiopaque material to substantially enhance fluoroscopic imaging of the filament.
  • Yet another object is to provide a case composite prosthesis in which a highly radiopaque material and a structural material cooperate to provide mechanical stability and enhanced fluoroscopic imaging, and further are selectively matched for compatibility as to their crystalline structure, coefficients of thermal expansion, and annealing temperatures.
  • a process for manufacturing a resilient body insertable composite filament includes the following steps: a. providing an elongate cylindrical core substantially uniform in lateral cross-section and having a core diameter, and an elongate tubular case or shell substantially uniform in lateral cross-section and having a case inside diameter, wherein one of the core and case is formed of a radiopaque material and the other is formed of a resilient material having an yield strength (0.2% offset) of at least 150,000 psi, wherein the core diameter is less than the interior diameter of the case, and the lateral cross-sectional area of the core and case is at most ten times the lateral cross-sectional area of the core; b.
  • the radiopaque material has a linear attenuation coefficient, at 100 KeV, of at least 25 cm " ⁇ .
  • the radiopaque material forms the core, and is at least as ductile as the case.
  • the outside diameter of the composite filament, before cold-working preferably is at most about six millimeters (about 0.25 inches).
  • the cold-working step can include drawing the composite filament serially through several dies, with each die plastically deforming the composite filament to reduce the outside diameter. Whenever a stage including one or more cold-working dies has reduced the cross-sectional area by at least 25%, an annealing step should be performed before any further cold-working.
  • the composite filament is heated to a temperature in the range of about 1900 - 2300° F. for a period depending on the filament diameter, typically in the range of several seconds to several minutes.
  • the core material and cladding (case) materials preferably are selected to have overlapping annealing temperature ranges, and similar coefficients of thermal expansion.
  • the core and case materials further can be selectively matched as to their crystalline structure and metallurgical compatibility.
  • the initial outside diameter of the composite structure typically is at least fifty millimeters (about two inches) in diameter.
  • the composite filament is subjected to temperatures in the annealing range while the outside diameter is substantially reduced, either by swaging or by pulltrusion, in successive increments until the outside diameter is at most about 6 millimeters (.25 inches).
  • the resulting filament is processed as before, in alternative cold-working and annealing stages.
  • the composite filament can be severed into a plurality of strands.
  • the strands are arranged in two oppositely directed sets of parallel helical windings about a cylindrical form, with the strands intertwined in a braided configuration to form multiple intersections.
  • the strands are maintained in a predetermined uniform tension, they are heated to a temperature in the range of about 700 - 1200° F., more preferably 900 - 1000° F., for a time sufficient to age harden the helical windings.
  • the result of this process is a resilient, body implantable prosthesis.
  • the prosthesis has a plurality of resilient strands, helically wound in two oppositely directed sets of spaced apart and parallel strands, interwoven with one another in a braided configuration.
  • Each of the strands includes an elongate core and an elongate tubular case surrounding the core.
  • a cross-sectional area of the core is at least ten percent of the cross-sectional area of the strand.
  • the core is constructed of a first material having a linear attenuation coefficient of at least 25 cm -1 at 100 KeV.
  • the case is constructed of a resilient second material, less ductile than the first material. -5-
  • the process can be employed to form a body compatible device comprising an elongate filament substantially uniform in lateral cross-section over its length and including an elongate cylindrical core and an elongate tubular case surrounding the core.
  • One of the core and case is constructed of a first material having an yield strength (0.2% offset) of at least twice that of the second material.
  • the other of the core and case is constructed of a second material being radiopaque and at least as ductile as the first material.
  • the core is constructed of tantalum for radio-opacity
  • the case is constructed of a cobalt-based alloy, e.g. as available under the brand names ⁇ lgiloy", “Phynox” and “MP35N”.
  • the "Elgiloy” and “Phynox” alloys contain cobalt, chromium, nickel, and molybdenum, along with iron. Either of these alloys is well matched with tantalum, in terms of overlapping annealing temperature ranges, coefficients of thermal expansion and crystalline structure.
  • the tantalum core and alloy case can be contiguous with one another, with virtually no formation of intermetallics.
  • an intermediate layer e.g. of tantalum, niobium, or platinum
  • tantalum, niobium, or platinum can be formed between the core and the case to provide a barrier against intermetallic formation.
  • a biocompatible coating or film can surround the case. Tantalum, platinum, iridium and their alloys, or stainless steels can be used for this purpose.
  • the composite filaments can be employed in constructing other implantable medical devices, e.g. vena cava filters, blood filters and thrombosis coils.
  • vena cava filters e.g. vena cava filters
  • blood filters e.g. vena cava filters
  • thrombosis coils e.g. vena cava filters
  • a resilient, body compatible prosthesis which, despite being sufficiently small for placement within blood vessels and similarly sized body cavities, has sufficient radio-opacity for fluoroscopic imaging based on the prosthesis materials themselves.
  • Figure 1 is a side elevation of a self-expanding stent constructed according to the present invention
  • Figure 2 is an end elevational view of the stent
  • Figure 3 is an enlarged partial view of one of the composite filaments forming the stent
  • Figure 4 is an enlarged sectional view taken along the line 4-4 in Figure 3;
  • Figures 5-9 schematically illustrate a process for manufacturing the stent;
  • Figure 10 schematically illustrates a swaging step of an alternative process for manufacturing the stent
  • Figure 11 is an end elevational view of an alternative embodiment filament
  • Figure 12 is an elevational view of several components of an alternative composite filament constructed according to the present invention.
  • Figure 13 is an end elevational view of the composite filament formed by the components shown in Figure 12;
  • Figure 14 is an end elevational view of another alternative embodiment composite filament. Detailed Description of the Preferred Embodiment
  • Stent 16 is of open mesh or weave construction, consisting of two sets of oppositely directed, parallel and spaced apart helically wound strands or filaments indicated at 18 and 20, respectively.
  • the sets of strands are interwoven in an over and under braided configuration to form multiple intersections, one of which is indicated at 22.
  • Stent 16 is illustrated in its relaxed state, i.e. in the configuration it assumes when subject to no external stresses.
  • the filaments or strands of stent 16 are resilient, permitting a radial compression of the stent into a reduced-radius, extended-length configuration suitable for transluminal delivery of the stent to the intended placement site.
  • stent 16 can have a diameter of about ten millimeters in the relaxed state, and is elastically compressed to a diameter of about 2 millimeters (.08 inches) and an axial length of about twice the axial length of the relaxed stent.
  • different applications call for different diameters.
  • Inelastic open-weave prostheses expandable for example by dilation balloons, provide an alternative to resilient prostheses.
  • Resilient or self-expanding prostheses often are preferred, as they can be deployed without dilation balloons or other stent expanding means.
  • Self-expanding stents can be preselected according to the diameter of the blood vessel or other intended fixation site. While their deployment requires skill in stent positioning, such deployme does not require the additional skill of carefully dilating the balloon to plastically expand the prosthesis to the appropriate diameter. Further, the self-expanding stent remains at least slightly elastically compressed after fixation, and thus has a restoring force which facilitates acute fixation.
  • a plastically expanded stent must rely on the restoring force of deformed tissue, or on hooks, barbs, or other independent fixation elements.
  • materials forming the strands for filaments must be strong and resilient, biocompatible, and resistant to fatigue and corrosion.
  • Vascular applications require hemocompatibility as well.
  • materials meet these needs including stainless "spring” steels, and certain cobalt-based alloys: more particularly two alloys including cobalt, chromium, iron, nickel and molybdenum sold under the brand names "Elgiloy” (available from Carpenter Technology Corporation of Reading, Pennsylvania) and “Phynox” (available from Metal Imohy of Imphy, France), respectively.
  • Another suitable cobalt-chromium alloy is available under the brand name "MP35N” from Carpenter Technology Corporation of Reading, Pennsylvania.
  • the filaments can have a diameter of about 0.1 millimeter (.004 inches), with adjacent parallel filaments spaced apart from one another by about 1-2 millimeters (.04-.08 inches) when the stent is in the relaxed state.
  • prosthesis 16 is substantially more amenable to fluoroscopic imaging, due to the construction of strands 18 and 20.
  • the strands cooperate to present a sufficiently radiopaque mass at the tangents of device 16 (parallel to the X-rays) for satisfactory real time imaging.
  • a filament 18a of he prosthesis is of composite construction, with a radiopaque core 24 surrounded by and concentric with an annular resilient case 26.
  • Core 24 is highly absorptive of X-rays, preferably having a linear attenuation coefficient of at least 25 (and more preferably at least 40) cm '1 at 100 KeV. Materials with relatively high atomic numbers and densities tend to have the necessary attenuation coefficients. More particularly, it has been found that materials with an atomic number (elements) or "effective" atomic number (based on a weighted average of elements in alloys or compounds) of at least fifty, and densities of at least 0.5 pounds per cubic inch, exhibit the required ability to absorb X-rays.
  • core 24 is preferably a ductile material so that it readily conforms to the shape of the case.
  • case 26 is formed of a highly resilient material, preferably with a yield strength (0.2% offset) of at least 150,000 psi. More preferably, the yield strength is at least 300,000 psi. Consequently, the mechanical behavior of composite filament 18a in terms of elastic deformation in response to external stresses is, essentially, the behavior of case 26.
  • the core and case materials should have the same or substantially the same linear coefficients of thermal expansion. Similarity of core and case materials in their crystalline structure is also an advantage.
  • the core and case materials should have an overlap in their annealing temperature ranges, to facilitate manufacture of the filaments according to the process to be explained.
  • core 24 is formed of tantalum
  • case 26 is formed of a cobalt-based alloy, more particularly Elgiloy (brand) alloy.
  • Tantalum is a ductile metal having an atomic number of 73 and a density of about 0.6 pounds per cubic inch. Its linear attenuation coefficient, at 100 KeV, is 69.7 cm " ⁇
  • the Elgiloy alloy includes principally cobalt and chromium, and has an effective atomic number of less than thirty and a density substantially less than 0.5 pounds per cubic inch. However, the alloy is body compatible, hemocompatible and highly resilient, with a yield strength (0.2% offset) of at least 350,000 psi, after cold working and age hardening.
  • Case 26 and core 24 thus cooperate to provide a prosthesis that can be viewed in vivo, and in real time.
  • the amount of core material in relation to the amount of case material must be sufficient to insure radio-opacity while maintaining the favorable mechanical characteristics of stent 16.
  • the area of core 24, taken along a transverse or lateral plane as illustrated in Figure 4 should be within the range of about ten percent to forty-six percent of the filament lateral cross-sectional area, i.e. the area of the combined case and core. Tantalum and the Elgiloy alloy are well matched, in that the materials have similar linear coefficients of thermal expansion (3.6 x 10 "6 per degree F.
  • Platinum and platinum alloys (e.g. platinum iridium) also are suitable as materials for core 24.
  • the atomic number of platinum is 78, and its density is 0.775 pounds per cubic inch. Its linear attenuation coefficient at 100 MeV is 105 cm “1 .
  • the linear coefficient of thermal expansion for platinum is about 4.9 x 10 "6 per degree F.
  • platinum is structurally more compatible with the Elgiloy alloy, and more effectively absorbs X-rays. Accordingly, platinum is particularly well suited for use in prostheses formed of small diameter filaments.
  • radiopaque core 24 examples include gold, tungsten, iridium, rhenium, ruthenium, and depleted uranium.
  • Other materials suitable for case 26 include other cobalt-based alloys, e.g. the
  • Cobalt-chromium and cobalt-chromium-molybdenum orthopedic type alloys also can be employed, as well as alloys of titanium-aluminum- vanadium.
  • the MP35N alloy is widely available, and has a potential for better fatigue strength due to improved manufacturing techniques, particularly as to the vacuum melting process.
  • the titanium-aluminum-vanadium alloys are highly biocompatible, and have more moderate stress/strain responses, i.e. lower elastic moduli.
  • Composite filaments such as filament 18a are manufactured by a drawn filled tubing (DFT) process illustrated schematically in Figures 7-9.
  • the DFT process can be performed, for example, by Fort Wayne Metals Research Products corporation of Ft. Wayne, Indiana.
  • the process begins with insertion of a solid cylinder or wire 28 of the core material into a central opening 30 of a tube 32 of the case material.
  • Core wire 28 and tubing 32 are substantially uniform in transverse or lateral sections, i.e. sections taken perpendicular to the longitudinal or axial dimension.
  • tube 32 can have an outer diameter d. of about 0.102 inch (2.6 mm) and an inner diameter d2 (diameter of opening 30) of about .056 inches (1.42 mm).
  • Core or wire 28 has an outer diameter d3 slightly less than the tube inner diameter, e.g. .046 inches (1.17 mm).
  • the wire outer diameter is sufficiently close to the tubing inner diameter to insure that core or wire 28, upon being inserted into opening 30, is substantially radially centered within the tubing.
  • the interior tubing diameter must exceed the core outside diameter sufficiently to facilitate insertion of the wire into an extended length of wire and tubing, e.g. at least twenty feet.
  • tubing inner diameter and the core outer diameter vary with the materials involved.
  • platinum as compared to tantalum has a smoother exterior finish when formed into the elongate wire or core.
  • the outer diameter of a platinum wire can more closely approximate the inner diameter of the tube.
  • the optimum diameter values vary with the materials involved, and the expected length of the composite filament.
  • insertion of the core into the tube forms a composite filament 34, which then is directed through a series of alternating cold-working and annealing steps, as indicated schematically in Figure 6. More particularly, composite filament 34 is drawn through three dies, indicated at 36, 38, and 40, respectively.
  • composite filament 34 is cold-worked in radial compression, causing the case tube 32 and the tantalum core wire 28 to cold flow in a manner that elongates the filament while reducing its diameter.
  • case tube 32 is elongated and radially reduced to a greater extent than core wire 28, due to the minute radial gap that allowed the insertion of the core into the tube.
  • the radial gap is closed rapidly as the filament is drawn through die 36, with subsequent pressure within die 36 and the remaining dies cold-working both the core and case together as if they were a single, solid filament.
  • the cold-working within all dies forms a pressure weld along the entire interface of the core and case, to form a bond between the core and case material.
  • the cold-working induces strain hardening and other stresses within the filament.
  • respective heating stages are provided, i.e. furnaces 42, 44 and 46, one heating stage to follow each cold- working die.
  • composite filament 34 is heated to a temperature in the range of from about 1900 to about 2300° F., or more preferably 2000 - 2150° F.
  • substantially all of the induced stresses are removed from the case and core, to permit further cold-working.
  • Each annealing step is accomplished in a brief time, e.g. in as few as one to fifteen seconds at annealing temperature, depending on the size of composite filament 34. While Figure 6 illustrates one cold-working stage and annealing stage, it is to be understood that the appropriate number of stages is selected in accordance with the final filament size, the desired degree of cross-sectional area reduction during the final cold-working stage, and the initial filament size prior to cold-working. In connection with composite filament 34, a reduction of lateral cross-sectional area in the range of about forty percent to eighty percent is preferred, and a range of about fifty- five percent to sixty-five percent is highly preferred.
  • the successive cold-working and annealing steps give rise to the need for matching the core and case materials, particularly as to their coefficients of thermal expansion, elastic moduli in tension, annealing temperature ranges, total elongation capacities, and also as to their crystalline structure.
  • a good match of elastic moduli, elongation, and thermal expansion coefficients minimizes the tendency for any ruptures or discontinuities along the core/case interface as the composite filament is processed.
  • Crystalline structures should be considered in matching core and case materials.
  • the Elgiloy alloy, and other materials used to form case tube 32 commonly experience a transformation between the cold-working and aging steps, from a face centered cubic crystalline structure to a hexagonal close packed crystalline structure. The Elgiloy alloy experiences shrinkage as it undergoes this transformation.
  • composite filament 34 is formed into the shape intended for the device incorporating the filament.
  • several filaments or strands 34a-e are helically wound about a cylindrical form 48 and held in place at their opposite ends by sets of bobbins 50a-e and 52a-e.
  • Strands 34a-e can be individually processed, or individual segments of a single annealed and cold-worked composite filament, cut after the final cold-working stage.
  • the filaments cooperate to form one of the two oppositely directed sets of spaced apart and parallel filaments that form a device such as stent 16. While only one set of filaments is shown, it is to be understood that a corresponding group of filaments, helically wound and intertwined about form 48 in the opposite direction, are supported by corresponding bobbins at the opposite filament ends.
  • a useful prosthesis depends, in part, upon correctly supporting the filaments.
  • the filaments are maintained in tension, and it is important to select the appropriate tensile force and apply the tensile force uniformly to all filaments. Insufficient tensile force may allow wire cast or lift effects to cause the individual filaments to depart from their helical configuration when released from the bobbins, and the braided structure of the stent may unravel.
  • Figure 9 illustrates two filaments 34a and 54a, one from each of the oppositely wound filament sets, supported by respective bobbins 50a/52a and 56a/58a in a furnace 60 for age hardening in a vacuum or protective atmosphere.
  • Age hardening is accomplished at temperatures substantially lower than annealing, e.g. in the range of about 700 - 1200°F., more preferably 900 - 1000°F.
  • the filaments overly one another to form several intersections, one of which is indicated at 62. When the filaments are properly tensioned, slight impressions are formed in the overlying filament at each intersection.
  • the elastic modulus is increased by at least 10% and the yield strength (0.2% offset) and tensile strength are each increased by at least 20%.
  • a substantially larger and shorter composite filament 64 e.g. six inches long with a diameter of approximately ten cm
  • Figure 10 schematically illustrates two swaging dies 66 and 68, which may be used in the course of a hot working billet reduction process. Of course, any appropriate number of swaging dies may be employed.
  • the diameter reduction can be accomplished by extrusion/pulltrusion at each stage.
  • the composite structure or filament can be further processed by drawing it through dies and annealing, as illustrated in Figure 6 for the previously discussed process. As before, the composite filament is ready for selective shaping and age hardening after the final cold-working stage.
  • the swaging or pulltrusion approach involves substantially increased hot and cold-working of the composite structure or filament, and the initial assembling of the core into the case or shell tubing is easier.
  • the structure is subjected to annealing temperatures for a substantially longer time, e.g. half an hour to an hour, as opposed to the one to fifteen second anneal times associated with the process depicted in Figure 6. Consequently, particular care must be taken to avoid combinations of core and case materials with tendencies for intermetallic formation along the core/case interface. Further, the required hot working of the larger billet may not afford the same degree of metallurgical grain refinement.
  • the preferred composite filaments have: (1) sufficient radio-opacity to permit in vivo viewing; (2) the preferred mechanical properties; and (3) a sufficiently low cost.
  • the interrelationship of these factors requires that all three be taken into account in determining filament size, relationship of core 24 to case 26 as to size, and materials selected for the core and case.
  • core 24 should be at least about 0.0015 inches in diameter, if a stent constructed of such filament is to be visible using conventional radiographic imaging equipment.
  • structural requirements particularly elasticity for a self-expanding stent
  • the visibility requirement effectively imposes a minimum diameter upon case 26 as well as core 24.
  • appropriate selection of core and casing materials can reduce the required minimum diameters.
  • potential substitute materials should be considered in view of their impact on cost - not only the material cost per se, but also as to the impact of such substitution on fabrication costs.
  • the core material is tantalum
  • the casing is constructed of the Elgiloy brand cobalt-based alloy.
  • the maximum outer diameter of the composite filament is about 0.150 mm, or about 0.006 inches.
  • Elgiloy filaments of this diameter or larger may be sufficiently radiopaque without a core of tantalum or other more radiopaque material.
  • radio-opacity is improved with a tantalum core, and likewise with a core of a tantalum-based alloy, platinum, platinum-based alloy, tungsten, a tungsten-based alloy or combination of these constituents.
  • the preferred core size varies with the filament diameter.
  • the core should contribute at least about one-third of the cross-sectional area of the composite filament.
  • Composite filaments of this structure have core diameters in the range of 0.037-0.05 mm (0.0015-0.002 inches), with filament diameters up to about 0.135 mm or about 0.0055 inches.
  • the core is formed of a platinum-10% nickel alloy, i.e. 90% platinum and 10% nickel by weight. While the preferred proportion of nickel is 10%, satisfactory results can be obtained with nickel ranging from about 5% to about 15% of the alloy.
  • the case is constructed of the Elgiloy alloy.
  • the platinum-nickel alloy as compared to pure tantalum, has superior radiographic and structural properties. More particularly, the alloy has a greater density, combined with a higher atomic number factor (z) for a 10-20% improvement in radio-opacity. Further as compared to tantalum, the alloy is more resistant to fatigue and thus better withstands processes for fabricating stents and other devices.
  • a core formed of a platinum-nickel alloy can constitute up to about 40% of the total filament cross-sectional area. Consequently the alloy is particularly well suited for constructing extremely fine filaments.
  • This structure of composite filament is suitable for constructing stents having diameters (unstressed) in the range of about 3.5-6 mm.
  • purity of the elements and alloys is important. Accordingly, high purity production techniques, e.g. custom melting (triple melting techniques and electron beam refining) are recommended to provide high purity Elgiloy alloy seamless tubing.
  • a third filament structure involves an Elgiloy case and a core formed of a tantalum-10% tungsten alloy, although the percentage of tungsten can range from about 5% to about 20%.
  • the tantalum ⁇ ungsten alloy is superior to tantalum in terms of mechanical strength and visibility, and costs less than the platinum-nickel alloy.
  • case 26 is formed of the Elgiloy alloy
  • core 24 is formed of a platinum-20 to 30% iridium alloy.
  • the platinum-iridium alloy can include from about 5 to about 50% iridium.
  • the platinum-iridium alloy may exhibit less resistance to fatigue. This is due in part to segregation which may occur during cooling of an alloy containing 30% (by weight) or more iridium, due to the relatively high melting point of iridium. Also, hot working may be required if the alloy contains more than 25% iridium, thereby making final cold reduction of the composite difficult.
  • a fifth filament structure employs an Elgiloy alloy case and a core of a platinum- tungsten alloy having tungsten in the range of about 5-15%, and more preferably 8%.
  • the radio-opacity of this alloy is superior to the platinum-nickel alloy and it retains the favorable mechanical characteristics.
  • casing 26 is constructed of a titanium-based alloy. More particularly, the alloy can be an alloy known as "grade 10" or "Beta 3" alloy, containing titanium along with molybdenum at 11.5%, zirconium at 6%, and tin at 4.5%. Alternatively, the titanium-based alloy can include about 13% niobium, and about 13% zirconium.
  • Core 24 can be formed of tantalum. More preferably, the core is formed of the platinum-10% nickel alloy. In this event, a barrier of tantalum should be formed between the core and case, as is discussed in connection with Figures 12 and 13.
  • the titanium-based alloy case is advantageous, particularly to patients exhibiting sensitivity to the nickel in the Elgiloy alloy, and may further be beneficial since it contains neither cobalt nor chrome. Also, because of the lower modulus of elasticity of the titanium-based alloy (as compared to Elgiloy), stents or other devices using the titanium-based alloy exhibit a more moderate elastic response upon release from a deployment catheter or other device. This may tend to reduce vascular neointimal hyperplasia and consequent restenosis.
  • the lower elastic modulus results in a less favorable matching of the case and core as to elasticity.
  • the proportion of core material to case material must be reduced.
  • this construction is suitable for filaments having diameters in the range of about 0.10-0.30 mm.
  • core 24 is constructed of a tungsten-based alloy including rhenium at 5-40 weight percent. More preferably, the alloy includes rhenium at about 25 percent by weight.
  • Further preferred materials for core 24 include alloys of about 85-95 weight percent platinum and about 5-15 weight percent nickel; alloys including about 50-95 weight percent platinum and about 5-50 weight percent iridium; alloys including at least 80 weight percent tantalum and at most 20 weight percent tungsten; and alloys including at least 60 weight percent tungsten and at most 40 weight percent rhenium.
  • Further suitable case materials are alloys including about 30-55 weight percent cobalt, 15-25 weight percent chromium, up to 40 weight percent nickel, 5-15 weight percent molybdenum, up to 5 weight percent manganese, and up to 25 weight percent iron.
  • the material should have a yield strength of at least 150,000 psi (0.2% offset). While less preferred, the case material can have a yield strength of at least 100,000 psi (0.2% offset).
  • Figure 11 is an end elevation of a composite filament 74 including a central core 76 of a structural material such as the Elgiloy alloy, surrounded by a radiopaque case 78, thus reversing the respective functions of the core and case as compared to composite filament 34.
  • Composite filament 74 as compared to filament 34, presents a larger and less refractive radiopaque profile for a given composite filament diameter.
  • Composite filament 74 is more difficult to manufacture than filaments that employ the structural material as the case.
  • Figures 12 and 13 show a further alternative composite filament 80, consisting of a central radiopaque core 82, an outer annular structural case 84, and an intermediate annular layer 86 between the core and the case.
  • Intermediate layer 86 provides a barrier between the core and case, and is particularly useful in composite filaments employing core and case materials that would be incompatible if contiguous, e.g. due to a tendency to form intermetallics.
  • Materials suitable for barrier layer 86 include tantalum, niobium and platinum.
  • the core, barrier layer and case can be provided as a cylinder and two tubes, inserted into one another for manufacture of the composite filament as explained above.
  • Figure 14 illustrates another alternative embodiment composite filament 88 having a central radiopaque core 90, a structural case 92, and a relatively thin annular outer cover layer 94.
  • Composite filament 88 is particularly useful when the selected mechanical structure lacks satisfactory biocompatibility, hemocompatibility, or both.
  • cover layer 94 Suitable materials for cover layer 94 include tantalum, platinum, iridium, niobium, titanium and stainless steel.
  • the composite filament can be manufactured as explained above, beginning with insertion of the radiopaque core into the structural case, and in turn, inserting the case into a tube formed of the cover material.
  • cover layer 94 can be applied by a vacuum deposition process, as a thin layer (e.g. from ten to a few hundred microns) is all that is required.
  • the following examples illustrate formation of composite filaments according to the above-disclosed processes. Example 1
  • An elongate tantalum core having a diameter of 0.46 inches (1.17 mm) was assembled into an Elgiloy alloy case having an outer diameter of 0.102 inches (2.6 mm) and an inner diameter of .056 inches (1.42 mm). Accordingly, the lateral cross-sectional area of the tantalum core was about 25% of the composite filament lateral cross- sectional area.
  • Composite filaments so constructed were subjected to 5-6 alternating stages of cold-working and annealing, to reduce the outer diameters of the composite filaments to values within the range of .004-.0067 inches.
  • the tantalum core diameters were reduced to values in the range of .002-.0034 inches.
  • the composite filaments were formed into a stent suitable for biliary applications, and age hardened for up to five hours, at temperatures in the range of 900-1000° F.
  • the resulting composite filaments were processed through about six cold-working and annealing cycles as in the first example, to reduce the outer filament diameter to values within the range of
  • the core thus constituted 43% of the filament lateral cross-sectional area.
  • the resulting filaments were formed into a small vascular stent, and age hardened for approximate ⁇ three hours.
  • Composite filaments were constructed and processed substantially as in example 2, except that the core was formed of a platinum nickel alloy, with nickel 10% by weight.
  • Example 4
  • the composite filaments were constructed and processed as in examples 2 and 3, except that the core was formed of tantalum, and the case was formed of MP35N alloy, and the cold-working stages reduced the filament outer diameter to values in the range of .00276-.0047 inches.
  • the resulting stents exhibited satisfactory elasticity and were readily fluoroscopically imaged in real time.
  • the device has an additional layer covering the case.
  • Possible materials for the additional layer include tantalum, gold, titanium, and platinum.
  • the additional layer preferably has a thickness in the range of about 0.005-5.0 microns, and can be applied by methods such as thin clad overlay co-drawing, electrochemical deposition of the metal after fabrication of the composite filament, ion implantation (such as physical vapor deposition and ion beam deposition), and sputter coating.
  • the additional layer is a metal having an electronegative surface such as tantalum.

Abstract

Un extenseur compatible pour être inséré dans le corps humain est formé de multiples filaments disposés en deux ensembles d'enroulements hélicoïdaux opposés entrelacés selon une configuration tressée. Chaque filament est un matériau composite comprenant une partie centrale (24) et une enveloppe (26) entourant la partie centrale (24). Dans une version davantage préférée, la partie centrale est constituée d'un matériau radiopaque et relativement ductile, tel que le tantale ou le platine. L'enveloppe externe (26) est formée d'un matériau relativement élastique, tel qu'un alliage à base de cobalt/chrome. Les bonnes caractéristiques mécaniques de l'extenseur sont déterminées par l'enveloppe (26) alors que la partie centrale (24) permet in vivo la visualisation de l'extenseur. Les filaments composites sont obtenus par un procédé de formation de tubes, remplis, étirés dans lesquel la partie centrale (24) est insérée dans une enveloppe tubulaire (26) d'un diamètre sensiblement supérieur au diamètre final, prévu, du filament. Le filament composite est formé à froid en plusieurs étapes afin de réduire son diamètre, et recuit entre des étapes successives de formage à froid. Après l'étape de formage final, le filament composite est formé selon une configuration désirée et durci par vieillissement. D'autres matériaux composites ont une couche barrière intermédiaire (86) placée entre l'enveloppe (26) et la partie centrale (24), une couche de couverture biocompatible entourant l'enveloppe (26), et une enveloppe radiopaque (26) entourant une partie centrale structurale (24).
PCT/IB1995/000253 1994-05-09 1995-04-10 Extenseur composite plaque WO1995030384A2 (fr)

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CA002188429A CA2188429C (fr) 1994-05-09 1995-04-10 Extenseur composite plaque
JP52880295A JP3415158B2 (ja) 1994-05-09 1995-04-10 クラッド複合ステント
MX9605485A MX9605485A (es) 1995-04-10 1995-04-10 Implante compuesto recubierto.
EP95913307A EP0758870A1 (fr) 1994-05-09 1995-04-10 Extenseur composite plaque

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US08/239,595 1994-05-09

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WO1997013475A1 (fr) * 1995-10-11 1997-04-17 Schneider (Usa) Inc. Prothese composite tressee
EP0809998A2 (fr) * 1996-05-28 1997-12-03 Cordis Corporation Endoprothèse en matériau composite
US5728042A (en) * 1995-06-22 1998-03-17 Schneider (Europe) A.G. Medical appliance for ionizing radiation treatment having radiopaque markers
EP0847733A1 (fr) * 1996-12-10 1998-06-17 BIOTRONIK Mess- und Therapiegeräte GmbH & Co Ingenieurbüro Berlin Stent
US5888201A (en) * 1996-02-08 1999-03-30 Schneider (Usa) Inc Titanium alloy self-expanding stent
EP0947204A2 (fr) * 1998-03-30 1999-10-06 Cordis Corporation Endoprothèse en matériau composite
NL1011779C2 (nl) * 1999-04-13 2000-10-16 Elephant Dental Bv Biomedisch hulpmiddel of implantaat.
WO2002053202A1 (fr) * 2001-01-05 2002-07-11 Gerd Hausdorf Implants medicaux metalliques degradables par corrosion
WO2003082362A3 (fr) * 2002-03-22 2004-01-15 Scimed Life Systems Inc Materiau de stent compatible aux rayons x et a l'irm
WO2004022122A3 (fr) * 2002-09-09 2004-05-13 Scimed Life Systems Inc Dispositifs medicaux
EP0857470B1 (fr) * 1997-01-09 2006-07-19 Sorin Biomedica Cardio S.R.L. Procédé de production d'un stent pour angioplastie
US7452502B2 (en) 2005-03-03 2008-11-18 Icon Medical Corp. Metal alloy for a stent
EP2056742A2 (fr) * 2006-07-24 2009-05-13 Existent, Inc. Modèles, matériaux et procédés de fabrication d'endoprothèses
US7540995B2 (en) 2005-03-03 2009-06-02 Icon Medical Corp. Process for forming an improved metal alloy stent
US7540994B2 (en) 2005-03-03 2009-06-02 Icon Medical Corp. Process for forming an improved metal alloy stent
US7604662B2 (en) 2007-07-13 2009-10-20 Boston Scientific Scimed, Inc. Endoprostheses containing boride intermetallic phases
WO2008100852A3 (fr) * 2007-02-13 2009-12-03 Abbott Cardiovascular Systems Inc. Alliages radio-opaques compatibles avec l'irm à utiliser dans les dispositifs médicaux
US7727273B2 (en) 2005-01-13 2010-06-01 Boston Scientific Scimed, Inc. Medical devices and methods of making the same
US7879367B2 (en) 1997-07-18 2011-02-01 Alfons Fischer Metallic implant which is degradable in vivo
US8398702B2 (en) 2007-06-29 2013-03-19 Boston Scientific Scimed, Inc. Molybdenum endoprostheses
US8398916B2 (en) 2010-03-04 2013-03-19 Icon Medical Corp. Method for forming a tubular medical device
EP1404391B2 (fr) † 2001-03-30 2014-01-15 Boston Scientific Limited Alliage d'acier inoxydable et de platine et stents radio-opaques
EP3165238A1 (fr) * 2015-11-04 2017-05-10 Biotronik AG Marqueur de radiographie pour une endoprothese
US10610231B2 (en) 2008-05-02 2020-04-07 Sequent Medical, Inc. Filamentary devices for treatment of vascular defects
US10813645B2 (en) 2013-08-16 2020-10-27 Sequent Medical, Inc. Filamentary devices for treatment of vascular defects
US10907283B2 (en) 2011-10-17 2021-02-02 Sequent Medical, Inc. Braiding mechanism and methods of use
US10939914B2 (en) 2013-08-16 2021-03-09 Sequent Medical, Inc. Filamentary devices for the treatment of vascular defects
US11141296B2 (en) 2012-04-26 2021-10-12 Medtronic Vascular, Inc. Radiopaque enhanced cobalt alloy for stents
US11179159B2 (en) 2007-06-04 2021-11-23 Sequent Medical, Inc. Methods and devices for treatment of vascular defects
US11291453B2 (en) 2019-03-15 2022-04-05 Sequent Medical, Inc. Filamentary devices having a flexible joint for treatment of vascular defects
US11317921B2 (en) 2019-03-15 2022-05-03 Sequent Medical, Inc. Filamentary devices for treatment of vascular defects
US11559309B2 (en) 2019-03-15 2023-01-24 Sequent Medical, Inc. Filamentary devices for treatment of vascular defects
US11678886B2 (en) 2014-04-14 2023-06-20 Microvention, Inc. Devices for therapeutic vascular procedures
US11766506B2 (en) 2016-03-04 2023-09-26 Mirus Llc Stent device for spinal fusion
US11779685B2 (en) 2014-06-24 2023-10-10 Mirus Llc Metal alloys for medical devices

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Cited By (49)

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Publication number Priority date Publication date Assignee Title
US5728042A (en) * 1995-06-22 1998-03-17 Schneider (Europe) A.G. Medical appliance for ionizing radiation treatment having radiopaque markers
WO1997013475A1 (fr) * 1995-10-11 1997-04-17 Schneider (Usa) Inc. Prothese composite tressee
US5888201A (en) * 1996-02-08 1999-03-30 Schneider (Usa) Inc Titanium alloy self-expanding stent
EP0809998A2 (fr) * 1996-05-28 1997-12-03 Cordis Corporation Endoprothèse en matériau composite
EP0809998A3 (fr) * 1996-05-28 1999-11-17 Cordis Corporation Endoprothèse en matériau composite
US6312456B1 (en) 1996-12-10 2001-11-06 Biotronik Mass-Und Therapiegeraete Gmbh & Co. Ingenieurbuero Berlin Biocompatible stent with radiopaque markers
EP0847733A1 (fr) * 1996-12-10 1998-06-17 BIOTRONIK Mess- und Therapiegeräte GmbH & Co Ingenieurbüro Berlin Stent
EP0857470B1 (fr) * 1997-01-09 2006-07-19 Sorin Biomedica Cardio S.R.L. Procédé de production d'un stent pour angioplastie
US7879367B2 (en) 1997-07-18 2011-02-01 Alfons Fischer Metallic implant which is degradable in vivo
EP0947204A2 (fr) * 1998-03-30 1999-10-06 Cordis Corporation Endoprothèse en matériau composite
EP0947204A3 (fr) * 1998-03-30 2000-12-20 Cordis Corporation Endoprothèse en matériau composite
WO2000061203A1 (fr) * 1999-04-13 2000-10-19 Elephant Dental B.V. Aide biomedicale ou implant
US7087077B1 (en) 1999-04-13 2006-08-08 Elephant Dental Bv Biomedical aid or implant
NL1011779C2 (nl) * 1999-04-13 2000-10-16 Elephant Dental Bv Biomedisch hulpmiddel of implantaat.
WO2002053202A1 (fr) * 2001-01-05 2002-07-11 Gerd Hausdorf Implants medicaux metalliques degradables par corrosion
EP1404391B2 (fr) † 2001-03-30 2014-01-15 Boston Scientific Limited Alliage d'acier inoxydable et de platine et stents radio-opaques
WO2003082362A3 (fr) * 2002-03-22 2004-01-15 Scimed Life Systems Inc Materiau de stent compatible aux rayons x et a l'irm
WO2004022122A3 (fr) * 2002-09-09 2004-05-13 Scimed Life Systems Inc Dispositifs medicaux
US7938854B2 (en) 2005-01-13 2011-05-10 Boston Scientific Scimed, Inc. Medical devices and methods of making the same
US7727273B2 (en) 2005-01-13 2010-06-01 Boston Scientific Scimed, Inc. Medical devices and methods of making the same
US7648590B2 (en) 2005-03-03 2010-01-19 ICON International Systems, Inc. Metal alloy for a stent
US7540995B2 (en) 2005-03-03 2009-06-02 Icon Medical Corp. Process for forming an improved metal alloy stent
US7452502B2 (en) 2005-03-03 2008-11-18 Icon Medical Corp. Metal alloy for a stent
US7648591B2 (en) 2005-03-03 2010-01-19 Icon Medical Corp. Metal alloys for medical devices
US7540994B2 (en) 2005-03-03 2009-06-02 Icon Medical Corp. Process for forming an improved metal alloy stent
US7648592B2 (en) 2005-03-03 2010-01-19 Icon Medical Corp. Metal alloy for a stent
US7452501B2 (en) 2005-03-03 2008-11-18 Icon Medical Corp. Metal alloy for a stent
EP2056742A2 (fr) * 2006-07-24 2009-05-13 Existent, Inc. Modèles, matériaux et procédés de fabrication d'endoprothèses
EP2056742A4 (fr) * 2006-07-24 2010-03-31 Existent Inc Modèles, matériaux et procédés de fabrication d'endoprothèses
WO2008100852A3 (fr) * 2007-02-13 2009-12-03 Abbott Cardiovascular Systems Inc. Alliages radio-opaques compatibles avec l'irm à utiliser dans les dispositifs médicaux
US11179159B2 (en) 2007-06-04 2021-11-23 Sequent Medical, Inc. Methods and devices for treatment of vascular defects
US8398702B2 (en) 2007-06-29 2013-03-19 Boston Scientific Scimed, Inc. Molybdenum endoprostheses
US7604662B2 (en) 2007-07-13 2009-10-20 Boston Scientific Scimed, Inc. Endoprostheses containing boride intermetallic phases
US10610231B2 (en) 2008-05-02 2020-04-07 Sequent Medical, Inc. Filamentary devices for treatment of vascular defects
US8398916B2 (en) 2010-03-04 2013-03-19 Icon Medical Corp. Method for forming a tubular medical device
US11352724B2 (en) 2011-10-17 2022-06-07 Sequent Medical, Inc. Braiding mechanism and methods of use
US10907283B2 (en) 2011-10-17 2021-02-02 Sequent Medical, Inc. Braiding mechanism and methods of use
US11885053B2 (en) 2011-10-17 2024-01-30 Microvention, Inc. Braiding mechanism and methods of use
US11141296B2 (en) 2012-04-26 2021-10-12 Medtronic Vascular, Inc. Radiopaque enhanced cobalt alloy for stents
US11723667B2 (en) 2013-08-16 2023-08-15 Microvention, Inc. Filamentary devices for treatment of vascular defects
US10813645B2 (en) 2013-08-16 2020-10-27 Sequent Medical, Inc. Filamentary devices for treatment of vascular defects
US10939914B2 (en) 2013-08-16 2021-03-09 Sequent Medical, Inc. Filamentary devices for the treatment of vascular defects
US11678886B2 (en) 2014-04-14 2023-06-20 Microvention, Inc. Devices for therapeutic vascular procedures
US11779685B2 (en) 2014-06-24 2023-10-10 Mirus Llc Metal alloys for medical devices
EP3165238A1 (fr) * 2015-11-04 2017-05-10 Biotronik AG Marqueur de radiographie pour une endoprothese
US11766506B2 (en) 2016-03-04 2023-09-26 Mirus Llc Stent device for spinal fusion
US11291453B2 (en) 2019-03-15 2022-04-05 Sequent Medical, Inc. Filamentary devices having a flexible joint for treatment of vascular defects
US11317921B2 (en) 2019-03-15 2022-05-03 Sequent Medical, Inc. Filamentary devices for treatment of vascular defects
US11559309B2 (en) 2019-03-15 2023-01-24 Sequent Medical, Inc. Filamentary devices for treatment of vascular defects

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WO1995030384A3 (fr) 1995-12-07
CA2188429C (fr) 2000-10-31
JP3415158B2 (ja) 2003-06-09
EP0758870A1 (fr) 1997-02-26
JPH09506025A (ja) 1997-06-17

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