US20060004440A1 - Bioabsorbable marker having radiopaque constituents and method of using the same - Google Patents

Bioabsorbable marker having radiopaque constituents and method of using the same Download PDF

Info

Publication number
US20060004440A1
US20060004440A1 US10/978,231 US97823104A US2006004440A1 US 20060004440 A1 US20060004440 A1 US 20060004440A1 US 97823104 A US97823104 A US 97823104A US 2006004440 A1 US2006004440 A1 US 2006004440A1
Authority
US
United States
Prior art keywords
radiopaque
bioabsorbable
marker
medical device
stent
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US10/978,231
Inventor
Jonathan Stinson
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Boston Scientific Scimed Inc
Original Assignee
Boston Scientific Scimed 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
Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=25420033&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=US20060004440(A1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Application filed by Boston Scientific Scimed Inc filed Critical Boston Scientific Scimed Inc
Priority to US10/978,231 priority Critical patent/US20060004440A1/en
Publication of US20060004440A1 publication Critical patent/US20060004440A1/en
Assigned to BOSTON SCIENTIFIC SCIMED, INC. reassignment BOSTON SCIENTIFIC SCIMED, INC. CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: SCHNEIDER (USA) INC.
Assigned to SCIMED LIFE SYSTEMS, INC. reassignment SCIMED LIFE SYSTEMS, INC. MERGER (SEE DOCUMENT FOR DETAILS). Assignors: BOSTON SCIENTIFIC SCIMED, INC.
Assigned to BOSTON SCIENTIFIC SCIMED, INC. reassignment BOSTON SCIENTIFIC SCIMED, INC. CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: SCIMED LIFE SYSTEMS, INC.
Priority to US12/485,682 priority patent/US20090259125A1/en
Assigned to SCHNEIDER (USA) INC. reassignment SCHNEIDER (USA) INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: STINSON, JONATHAN S.
Abandoned legal-status Critical Current

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2/00Filters 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
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents 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
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12099Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder
    • A61B17/12109Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder in a blood vessel
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12131Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
    • A61B17/1214Coils or wires
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12131Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
    • A61B17/12168Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device having a mesh structure
    • A61B17/12172Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device having a mesh structure having a pre-set deployed three-dimensional shape
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/39Markers, e.g. radio-opaque or breast lesions markers
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2/00Filters 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
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/58Materials at least partially resorbable by the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00Materials 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
    • A61L31/14Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L31/148Materials at least partially resorbable by the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00Materials 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
    • A61L31/14Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L31/18Materials at least partially X-ray or laser opaque
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2/00Filters 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
    • A61F2/02Prostheses implantable into the body
    • A61F2/30Joints
    • A61F2002/30001Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
    • A61F2002/30003Material related properties of the prosthesis or of a coating on the prosthesis
    • A61F2002/3006Properties of materials and coating materials
    • A61F2002/30062(bio)absorbable, biodegradable, bioerodable, (bio)resorbable, resorptive
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2/00Filters 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
    • A61F2/02Prostheses implantable into the body
    • A61F2/30Joints
    • A61F2002/30001Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
    • A61F2002/30003Material related properties of the prosthesis or of a coating on the prosthesis
    • A61F2002/3006Properties of materials and coating materials
    • A61F2002/3008Properties of materials and coating materials radio-opaque, e.g. radio-opaque markers
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2210/00Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0004Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof bioabsorbable
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0058Additional features; Implant or prostheses properties not otherwise provided for
    • A61F2250/0096Markers and sensors for detecting a position or changes of a position of an implant, e.g. RF sensors, ultrasound markers
    • A61F2250/0098Markers and sensors for detecting a position or changes of a position of an implant, e.g. RF sensors, ultrasound markers radio-opaque, e.g. radio-opaque markers
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00Catheters; Hollow probes
    • A61M25/01Introducing, guiding, advancing, emplacing or holding catheters
    • A61M25/0105Steering means as part of the catheter or advancing means; Markers for positioning
    • A61M25/0108Steering means as part of the catheter or advancing means; Markers for positioning using radio-opaque or ultrasound markers

Definitions

  • This invention relates generally to a bioabsorbable marker having radiopaque constituents “bioabsorbable-radiopaque marker” for use on an implantable endoprosthesis such as a stent.
  • the bioabsorbable marker includes dispersable radiopaque constituents which are not bioabsorbable or degradable, but are excreted from the body or stored in the body.
  • Implantable endoprostheses including stents, stent-grafts, and grafts are used in percutaneous transluminal coronary angioplasty and in other medical procedures to repair and support diseased or damaged arteries and body lumens. Grafts are implanted to cover or bridge leaks or dissections in vessels. Stent-grafts are stents which generally have a porous coating attachment. Unsupported grafts are porous tubes which are typically implanted by surgical cut-down.
  • the surgical delivery device and implantable endoprosthesis may be visualized if they are radiopaque and offer radiographic contrast relative to the body.
  • radiographic contrast solution may be injected into the body lumen so that the lumen may be seen in the fluoroscopic image.
  • Implantable endoprosthesis In order for the Implantable endoprosthesis to be radiopaque, it must be made from a material possessing radiographic density higher than surrounding host tissue and have sufficient thickness to affect the transmission of x-rays to produce contrast in the image. Reference is made to the clad composite stent shown in U.S. Pat. No. 5,630,840.
  • An implantable endoprosthesis may be made of metals including tantalum, or platinum having relatively high radiographic densities. Other metals such as stainless steel, superalloys, nitinol, and titanium having lower radiographic densities may also be used. Reference is made to implantable devices shown in U.S. Pat. Nos. 4,655,771; 4,954,126; and 5,061,275.
  • An implantable polymeric endoprosthesis is generally radiolucent and does not possess sufficient radiographic density to be easily imaged by fluoroscopy.
  • polymers may be mixed with radiopaque filler materials prior to molding or extruding in order to enhance the radiographic density.
  • fillers may be used with polymers.
  • changes in the properties of the polymer may occur. For example, the additions of fillers may reduce the strength or ductility of the polymer.
  • bioabsorbable-radiopaque markers for use on implantable endoprostheses in order to improve radiopacity and the locatability of an endoprosthesis during various medical procedures.
  • Providing temporary radiopacity is especially advantageous for implantable endoprostheses having little or no radiopacity.
  • the bioabsorbable-radiopaque markers allow radiographic identification of one or more locations of interest on an implantable endoprosthesis.
  • Bioabsorbable-radiopaque markers in the fabric or covering materials of an implantable endoprosthesis are advantageous for indicating the location of the fabric or covering during implantation.
  • bioabsorbable-radiopaque markers may be used on the implantable endoprosthesis having little or no radiopacity. After implantation, the bioabsorbable-radiopaque marker may be absorbed, dissolved, or excreted from the body so as not to effect the function of the endoprosthesis.
  • a disadvantage of certain permanent radiopaque markers is that they may compromise structural integrity, may not be biocompatible or biostable, and may be more thrombogenic than the implantable endoprosthesis.
  • the bioabsorbable-radiopaque marker of the present invention advantageously allows most any implantable endoprosthesis to have temporary radiopacity over a predetermined portion of its structure, and advantageously assists with proper positioning and locatability of the implantable endoprosthesis in a body lumen.
  • the radiopaque property may be present only for a desired time period on an implantable endoprosthesis. For instance, once the implantable endoprosthesis is implanted, it may be more desirable to image with techniques such as ultrasound, magnetic resonance, and endoscopy and to avoid further radiation exposure to the patient. As the bioabsorbable polymer degrades, radiopaque material simultaneously or subsequently disperses into the body. The dispersion of the radiopaque material from the marker results in a loss of radiopacity in the marker. A predetermined rate of release of the radiopaque material may be designed into the bioabsorbable marker based on degradation of the polymer in the body or the design of the marker structure.
  • the bioabsorbable material in the bioabsorbable-radiopaque markers may include polymers or copolymers such as polylactide [poly-L-lactide (PLLA), poly-D-lactide (PDLA)], polyglycolide, polydioxanone, polycaprolactone, polygluconate, polylactic acid-polyethylene oxide copolymers, modified cellulose, collagen, poly(hydroxybutyrate), polyanhydride, polyphosphoester, poly(amino acids), poly(alpha-hydroxy acid) or related copolymers materials, each of which have a characteristic degradation rate in the body.
  • polylactide poly-L-lactide (PLLA), poly-D-lactide (PDLA)
  • polyglycolide polydioxanone
  • polycaprolactone polygluconate
  • polylactic acid-polyethylene oxide copolymers modified cellulose
  • collagen collagen
  • polyanhydride polyphosphoester
  • polyglycolide and polydioaxanone are relatively fast-bioabsorbing materials (weeks to months) and PLA is a relatively slow-bioabsorbing material (months to years).
  • mass degradation is completed with total absorption of the polymer endoprosthesis in about 1.5 to 3 years after implantation.
  • Bioabsorbable resins such as PLLA, PDLA, PGA and others are commerciallv available from several sources including PURAC America, Inc. of Lincolnshire, Ill. Radiopaque materials such as barium sulfate and bismuth trioxide are commerciallv available and compounded with the bioabsorbable resin by New England Urethane, Inc. of North Haven, Conn.
  • the bioabsorbable resin or bioabsorbable-radiopaque resin may be extruded into filament by Albany International Research Co. of Mansfield, Mass.
  • the bioabsorption rate of the marker may be designed to be fast for applications where acute radiopacity is desired such as during positioning and placement of the implant. Alternatively, the bioabsorption rate may be designed to be slower for applications where the implant must be radiographically imaged for at least a portion of its functional time, for example, in implants where healing may take months. Other bioabsorption rates are also possible.
  • the bioabsorption rate of the marker may be tailored by controlling the type of bioabsorbable polymer; chemical composition of the bioabsorbable polymer; molecular weight of the bioabsorbable polymer; thickness and density of the bioabsorbable polymer; surface area of the marker, exit area for the radiopaque material, and design of the marker structure.
  • the degradation products from the bioabsorbable marker and the dispersed radiopaque material are metabolized, excreted, or stored by the body.
  • Metabolism is the chemical process in living cells by which energy is provided for vital processes and activities and new material is assimilated to repair the waste. It is the sum of the processes by which a particular substance is handled in the living body.
  • Excretion is separation and elimination or discharge from the blood or tissues of useless, superfluous, or harmful material that is eliminated from the body.
  • the biocompatibility of absorbable polymers during degradation depends upon the rate of accumulation and how well the surrounding tissue or fluid buffers or metabolizes the degradation products. If the products are metabolizable, the rate at which this will occur is dependent upon the blood circulation in the tissue. A well-vascularized lumen wall could buffer and metabolize degradation products as they are released from the implant. This biological process is important to minimize adverse tissue reaction to the degrading implant.
  • the degradation products from PLLA and PGA are lactic and glycolic acid, respectively, which are normally present in the human body.
  • the acids are metabolized by cells around the implant.
  • the metabolization process is a citrate cycle which converts the acids to carbon dioxide which is respirated out of the body.
  • the radiopaque agents added to the bioabsorbable marker are generally insoluble in the body and thus are not metabolizable. If these materials are trapped within tissue, the host generally reacts by encapsulation and acceptance of the biologically inactive particles. If the material is released from the implant into systemic circulation, it will migrate with fluid flow until being excreted or collected and stored by organs or tissue.
  • the idea is to only have small amounts of the radiopaque substances in the implant by incorporating the discrete bioabsorbable-radiopaque marker rather than to load the entire implant with the radiopaque material. Minimization of the amount of radiopaque material which will be liberated from the marker upon absorption of the polymer must be considered when determining the loading percentage based on radiographic and mechanical properties.
  • the markers should include material having atomic elements of sufficiently high atomic number and be of sufficient thickness to provide sufficient radiopacity for imaging.
  • the bioabsorbable-radiopaque marker may have one or more hollow, cavity, or porous portions wherein radiopaque material may be disposed.
  • Attenuation is the change in the number of photons in the incident x-ray beam due to the interaction with an absorber.
  • To image an object implanted in the body it would be desirable to have the object attenuate x-rays more than body tissue, bone, and fat so that the difference in contrast will be obvious in a radiograph.
  • the difficulty in selecting a radiopaque material for surgical implants is that the material must have desirable radiographic characteristics and biocompatibility.
  • a substance which absorbs more x-rays can be deposited on or mixed in with the implant material. If the implant absorbs more x-rays than the surrounding medium (for example tissue in the body), it will be visible as a sharp change in contrast on an x-ray film or fluoroscopy image.
  • N/N 0 would be the fraction of incident x-ray energy that is transmitted through the absorber.
  • a more radiopaque material would have a lesser fraction of transmitted energy than a more radiolucent material. Therefore, to enhance the radiopacity of a material, such as the marker material, it would be desirable to select a material with high x-ray absorbing capability to minimize the fraction of transmitted energy.
  • This radiopacity capability is proportional to the linear attenuation coefficient and the thickness of the absorber material. The higher the attenuation coefficient of the absorber material for a given thickness, the more radiopaque the absorber will be. The attenuation produced by an absorber is dependent upon the number of electrons and atoms present in the absorber.
  • Radiopacity is therefore generally proportional to the atomic number (number of electrons in the atom) of the material.
  • Candidate materials for enhancing the radiopacity of surgical implants would have higher atomic numbers than the elements present in the body and would have to be biocompatible. The atomic number must be sufficiently high so that relatively small thickness of absorber material can be used in the body.
  • Table 1 describes a number of elements and their respective atomic numbers and certain linear attenuation coefficients.
  • the elements hydrogen, oxygen, carbon, and nitrogen are commonly found in the body and in polymers, so elements with higher atomic numbers than these should enhance the radiopacity of a polymer implant or marker.
  • Tantalum, zirconium, titanium, barium, bismuth, and iodine are known to be non-toxic in certain concentrations and thus are candidate elements for enhancing radiopacity of a polymer marker in an implant.
  • These elements can be added to the polymer in various loading percentages and the threshhold above which the loading causes unsatisfactory changes in the polymer characteristics can be determined through material and device testing.
  • the elements which can be added in quantities sufficient to enhance radiopacity and maintain an acceptable level of polymer properties and which are biocompatible could be utilized in markers.
  • the biocompatible elements with a range of atomic numbers of from about 22 to about 83 and having linear attenuation coefficients in the range of from about 10 to about 120 cm ⁇ 1 at 50 KeV should provide enough enhancement in radiopacity without excessive thickness being necessary to be useful in markers.
  • These elements would include at least titanium, vanadium, chromium, iron, cobalt, nickel, copper, bromine, zirconium, niobium, molybdenum, silver, iodine, barium, tantalum, tungsten, platinum, gold, and bismuth.
  • the preferred metallic elements for biocompatibility and radiopacity are titanium, zirconium, tantalum, and platinum.
  • the preferred organic elements for biocompatibility and radiopacity are bromine, iodine, barium, and bismuth.
  • Especially preferred elements are tantalum, platinum, barium, and bismuth because of their high atomic numbers and biocompatibility (atomic numbers from 56 to 83 and linear attenuation coefficients from 30 to 120). Tantalum and platinum are used as stent components and barium sulfate and bismuth trioxide are used as radiopaque enhancements for polymer catheters.
  • the bioabsorbable-radiopaque marker may be integrated into a subassembly or a finished implantable endoprosthesis during manufacture.
  • Radiopaque elongate elements may be braided together with non-radiopaque bioabsorbable elongate elements to form a tubular braided stent, or the bioabsorbable and radiopaque elongate elements may be woven into the finished-braided stent.
  • the bioabsorbable-radiopaque marker would advantageously add temporary radiopacity to an implantable endoprosthesis such that the temporary marker would not require a medical procedure for removal from the patient.
  • an implantable endoprosthesis and bioabsorbable-radiopaque marker system including an implantable endoprosthesis adapted to be disposed in a body lumen and at least one marker.
  • the marker having a proximal end, a distal end, and a thickness.
  • the marker including bioabsorbable material and radiopaque material and is disposed on or adjacent the endoprosthesis.
  • the marker is adapted to degrade in vivo whereby the bioabsorbable material is metabolized through or excreted from the body and the radiopaque material is excreted from or stored in the body.
  • the bioabsorbable material may include a polymer or copolymer.
  • the bioabsorbable material may include poly-L-lactide, poly-D-lactide, polyglycolide, polydioxanone, polycaprolactone, and polygluconate, polylactic acid-polyethylene oxide copolymers, modified cellulose, collagen, poly(hydroxybutyrate), polyanhydride, polyphosphoester, poly(amino acids), poly(alpha-hydroxy acid) and combinations thereof.
  • the radiopaque material may have a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • the marker may have an average thickness of from about 20 microns to about 500 microns and the radiopaque material includes at least one element with an atomic number of from about 22 to about 83.
  • the radiopaque material may include barium sulfate, bismuth trioxide, bromine, iodine, iodide, titanium oxide, zirconium oxide, tantalum, and combinations thereof.
  • the radiopaque material may be an oxide or salt material.
  • One of the bioabsorbable material or radiopaque material may be coated or compounded with the other and the radiopaque material may have a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • the marker may have a weight percent of the radiopaque material in the bioabsorbable material of from about 1% to about 80%.
  • the bioabsorbable material may consist of PLLA and the radiopaque material may consist of bismuth trioxide and the weight percent of the bismuth trioxide in the PLLA may be at least about 10%.
  • the bioabsorbable material may consist of PLLA and the radiopaque material may be barium sulfate and the weight percentage of the barium sulfate in the PLLA may be at least about 10%.
  • the marker may substantially degrades in less than about 3 years. “Substantial degradadation of the marker” means that the marker has lost at least 50% of its structural strength. It is preferable that the marker lose about 100% of its structural strength.
  • the bioabsorbable material may consist of polylactide and the radiopaque material may consist of barium sulfate, bismuth trioxide, iodine, iodide, and combinations thereof and the marker substantially degrades in from about 1 year to about 2 years.
  • the bioabsorbable material may include poly-L-lactide, poly-D-lactide, polyglycolide, and combinations thereof and the radiopaque material may include barium sulfate, bismuth trioxide, bromine, iodine, iodide, and combinations thereof and the marker substantially degrades in from about 3 months to about 1 year.
  • the bioabsorbable material may include polyglycolide, polygluconate, polydioxanone, and combinations thereof and the radiopaque material may include barium sulfate, bismuth trioxide, bromine, iodine, iodide, and combinations thereof and the marker substantially degrades in from about 1 week to about 3 months.
  • the marker may be a mono-filament, multi-filament, thread, ribbon, suture, and combinations thereof.
  • the marker may include one or more hollow, cavity, porous, and combinations thereof portions and the radiopaque material may be disposed therein.
  • the marker may have radiopacity for a predetermined amount of time.
  • the endoprosthesis may be a stent, stent-graft, graft, filter, occlusive device, or valve.
  • the endoprosthesis may have a tubular, radially expandable structure and axially flexible structure including a plurality of the elongate elements which are interwoven in a braid-like configuration.
  • the invention also relates to an implantable endoprosthesis and bioabsorbable-radiopaque marker system including an implantable endoprosthesis adapted to be disposed in a body lumen and at least one elongated marker.
  • the marker is adapted to be disposed on or adjacent the endoprosthesis.
  • the marker includes a proximal end, distal end, thickness, bioabsorbable material, and a radiopaque material having a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • the marker has at least one hollow, cavity, or porous portion where the radiopaque material may be disposed.
  • the bioabsorbable material at least partially contains the radiopaque material in the marker.
  • the radiopaque material may be a liquid, solid, powder, gel, particle, or combinations thereof.
  • the invention also relates to a method of marking an implantable endoprosthesis including: disposing at least one elongate marker on or adjacent to at least a portion of an implantable endoprosthesis.
  • the marker is from about 20 weight percent to about 99 weight percent of a bioabsorbable polymer and from about 1 weight percent to about 80 weight percent of a radiopaque material.
  • the radiopaque material includes liquid or particles, the particles having an average diameter less than about 200 microns and a maximum diameter less than about 400 microns.
  • the radiopaque material has a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV; disposing the endoprosthesis and marker in a delivery system; inserting the delivery system in a body lumen; deploying the endoprosthesis and marker from the delivery system into a body lumen; and allowing the polymer to bioabsorb or excrete and the radiopaque material to subsequently or simultaneously at least partially disperses from the endoprosthesis.
  • the invention also relates to a temporary bioabsorbable-radiopaque marker including a marker having an average thickness less than about 500 microns and consisting of a bioabsorbable material and a radiopaque material, the radiopaque material having a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • the marker is adapted to be disposed in a body lumen and degrade in vivo.
  • the marker may be elongate and have a proximal end and a distal end.
  • the invention also relates to a bioabsorbable-radiopaque marker including an elongate element adapted to be disposed in a body lumen and used as a surgical guide, the element including a bioabsorbable material, a radiopaque material, and combinations thereof.
  • the element has a weight percent, W, of the radiopaque material in the bioabsorbable material, and an average thickness, T, over the length of the elongate element.
  • the weight percent, W is equal to about:
  • the invention also relates to a marker including from about 20 weight percent to about 99 weight percent of a bioabsorbable polymer; and from about 1 weight percent to about 80 weight percent of a radiopaque material.
  • the radiopaque material includes at least one of a liquid or particle having an average particle diameter less than about 8 microns and a maximum particle diameter less than about 10 microns.
  • the radiopaque material has a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • the preferred average particle size is from about 3 microns to about 6 microns and a maximum particle size of 6 microns.
  • the average particle size may be from about 100 microns to about 150 microns and a maximum particle size of 400 microns.
  • FIG. 1 is a side view of stent delivery system having a bioabsorbable-radiopaque marker disposed on an implantable endoprosthesis;
  • FIG. 2 is a side view of the delivery system and a deployed implantable endoprosthesis in a body lumen;
  • FIGS. 3 a , 3 b , and 3 c are cross-sectional views of three alternative marker dispositions of the bioabsorbable-radiopaque marker on the implantable endoprosthesis at section 3 - 3 of FIG. 2 ;
  • FIG. 4 is a side view of a bioabsorbable-radiopaque marker disposed in a longitudinal pattern on a implantable endoprosthesis;
  • FIG. 5 is a side view of a bioabsorbable-radiopaque marker disposed in a helical pattern on a implantable endoprosthesis
  • FIG. 6 is a side view of a relatively flexible bioabsorbable-radiopaque marker
  • FIGS. 7 a - 7 e are cross-sectional views of five alternative bioabsorbable-radiopaque markers at section 7 - 7 of FIG. 6 ;
  • FIGS. 8 a - 8 c are side views of three alternative bioabsorbable-radiopaque markers
  • FIG. 9 is a side views of a porous bioabsorbable-radiopaque marker.
  • FIGS. 10 a - 10 d are side views of four elongate elements having radiopaque materials therein.
  • FIG. 11 is a side view illustrating one possible arrangement of discrete bioabsorbable-radiopaque markers disposed on an implantable endoprosthesis
  • FIG. 12 is the detail bounded by the dashed-line circle in FIG. 12 illustrating a bioabsorbable-radiopaque marker disposed around one implantable endoprosthesis wire crossing point;
  • FIG. 13 is a side view illustrating a discrete radiopaque marker
  • FIG. 14 illustrates the discrete bioabsorbable-radiopaque marker positioned on an embolization occlusion coil intravascular device.
  • FIG. 1 illustrating a stent delivery device 10 having one or more bioabsorbable-radiopaque markers 14 disposed in a helical pattern on an implantable endoprosthesis 16 .
  • the bioabsorbable-radiopaque marker 14 is disposed on the endoprosthesis 16 preferably before loading the assembly thereof into the outer tube of a delivery device 10 .
  • FIG. 2 illustrates an implantable endoprosthesis 16 having a bioabsorbable-radiopaque markers 14 disposed in a helical pattern thereon in a body lumen 12 .
  • Implantable endoprostheses 16 known in the art include stents, stent-grafts, grafts, filters, occlusive devices, valves, and combinations thereof, all may incorporate the bioabsorbable-radiopaque marker 14 .
  • FIGS. 3 a - 3 c illustrate three alternative locations on an implantable endoprosthesis 16 for disposing the bioabsorbable-radiopaque marker.
  • the bioabsorbable-radiopaque marker 14 may be disposed on portions of the inside surface 17 , outside surface 19 , or be inter-woven or inter-braided about and through the elongated elements of the implantable endoprosthesis 16 .
  • the bioabsorbable-radiopaque marker 14 may be disposed on the implantable endoprosthesis 16 in one or more predetermined lengths.
  • FIGS. 4 and 5 illustrating the bioabsorbable-radiopaque marker 14 disposed in two alternative patterns on the implantable endoprosthesis 16 .
  • FIG. 4 shows the bioabsorbable-radiopaque marker 14 interwoven through the filaments of the endoprosthesis 16 in a relatively longitudinal pattern.
  • the bioabsorbable-radiopaque marker 14 may be interwoven through the filaments of the endoprosthesis 16 in a relatively circumferential pattern.
  • FIG. 5 shows a marker 14 interwoven through the filaments of the endoprosthesis 16 in a relatively helical pattern.
  • Other patterns and dispositions of the bioabsorbable-radiopaque marker 14 on the endoprosthesis 16 are also possible.
  • One or more markers 14 may be temporarily disposed on the implantable endoprosthesis 16 to advantageously provide temporary radiopacity to predetermined locations on the implantable endoprosthesis 16 .
  • the bioabsorbable-radiopaque marker 14 may be disposed to one or more surfaces of the implantable endoprosthesis 16 with a relatively weak bioabsorbable adhesive or gelatin.
  • the bioabsorbable-radiopaque marker 14 may include elongate elements such as a ribbon, thread, filament, suture, or combinations thereof.
  • the bioabsorbable-radiopaque marker 14 may be braided to form a rope or cable.
  • the bioabsorbable-radiopaque marker 14 may adjust with the expansion of the implantable endoprosthesis 16 , and advantageously provide radiopacity and enhance the viewing of the implantable endoprosthesis 16 position or size during fluoroscopy.
  • the delivery device 10 may be removed from the body and the bioabsorbable-radiopaque marker 14 may remain on the implantable endoprosthesis 16 to be bioabsorbed, dissolved, dispersed, or excreted from the body.
  • the bioabsorbable-radiopaque marker 14 may be designed to remain on the implantable endoprosthesis 16 for a predetermined period of time if there is a need for follow-up angiography.
  • FIG. 6 illustrating a bioabsorbable-radiopaque marker 14 preferably made from a relatively flexible elongate polymeric material including radiopaque material containing at least one element with an atomic number of from about 22 to about 83.
  • the radiopaque material preferably has a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • FIGS. 7 a - 7 e illustrate alternative cross-sectional embodiments of the bioabsorbable-radiopaque marker 14 taken through the line 7 - 7 of FIG. 6 .
  • FIG. 7 a shows a substantially solid member
  • FIG. 7 b shows a hollow member
  • FIG. 7 c shows a member having pores extending radially into the member
  • FIG. 7 d shows a rectangular or ribbon member
  • FIG. 7 e shows a braided hollow member.
  • FIG. 7 e may also be a substantially solid braided member.
  • a composite bioabsorbable-radiopaque marker 14 may include a bioabsorbable polymer that is coated, compounded, filled, loaded, or mixed with a radiopaque substance such as iodide, iodine, zirconium oxide, barium sulfate, bismuth trioxide, or a related oxide or salt substance.
  • Composite radiopaque materials may contain at least one element having an atomic number, preferably, higher than about 22.
  • Other radiopaque materials may include gold, platinum, tantalum, metallic biomaterial alloys for coating, and small particles of these materials, preferably, less than 10 microns in size for compounding.
  • the weight percentage of radiopaque resins to bioabsorbable resins ranges from about 1 percent to about 80 percent.
  • the weight percentage of radiopaque metallic fillers to bioabsorbable resins ranges from about 1 percent to about 40 percent.
  • the preferred weight percentage of bismuth trioxide and barium sulfate in PLLA filament is a minimum of about 10%.
  • Preferred embodiments of the bioabsorbable-radiopaque marker are set forth below in Table 2.
  • the column for marker type in Table 2 contains a description of the physical aspects of the marker such as a strand threaded in and out of the braided stent interstices, following a wire helix or in and out of the braided stent interstices around the circumference, or in and out of the braided stent interstices in a straight line in the axial orientation.
  • An interstice is the location where two stent wires in the braid cross over one another.
  • the function of the marker is described in Table 2 to indicate how the marker is used in the endoprosthesis, for example, to indicate the ends of a stent or to allow radiographic visualization of the stent changing from a constrained condition to an expanded condition as it is deployed.
  • a list of devices where the marker could be incorporated is provided in Table 2 and generally contains various types of intraluminal endoprostheses.
  • the preferred metal radiopaque constituents (Ta, Pt, Zr, Ti) are known to be biocompatible and have relatively high atomic numbers and linear attenuation coefficients. These elements would be added to the bioabsorbable polymer to make the material radiopaque and suitable for radiographic marking.
  • the adjacent column, Metal Radiopaque Constituent Loading, Weight % indicates the preferred range of loading of the metal radiopaque constituents into the bioabsorbable polymer to make it sufficiently radiopaque, such as from about 1 to about 20 weight percent tantalum or platinum compounded or coated onto the polymer.
  • the same type of information is given in the next two columns for organic radiopaque constituents.
  • the marker may be made with either metal or organic constituents, with metal being preferred for thin markers and organics being more appropriate for thicker markers where higher loadings can be tolerated (so as to not weaken the marker significantly).
  • the last two columns in the table contain preferred absorbable polymers for the marker matrix material.
  • PLLA and PDLA are preferred for slow-absorbing markers, because the degradation rate of these polymers is rather slow (months to years).
  • PGA and polydioxanone are preferred for fast-absorbing markers because the degradation rate of these polymers is rather fast (weeks to months).
  • the markers of the invention can be segregated into types; threaded and discrete bioabsorbable-radiopaque markers.
  • a threaded marker is generally a strand or strands of material having radiopacity which is incorporated within the implantable device by interweaving or interbraiding the strand through the struts or wires of the endoprosthesis.
  • a discrete bioabsorbable-radiopaque marker is generally a bioabsorbable-radiopaque polymer strand of material which is securely attached to a localized region of the implantable device and does not significantly extend over a large portion of the device.
  • An example of a threaded marker in a braided wire tubular stent is a bioabsorbable-radiopaque polymer strand loaded with a radiopaque constituent that is woven in and out of the wire crossing points following the helical path of one individual wire strand in the stent.
  • An example of a discrete bioabsorbable-radiopaque marker is a coil, knot, or ring of a bioabsorbable-radiopaque polymer strand around a feature of a stent, such as a stent wire crossing point.
  • the strand is wrapped, coiled, or tied around the stent wire and thereby is mechanically attached to the device.
  • the strand ends are clipped off such that the marker is present as a small, tight ring around a feature of the stent.
  • the stent with the attached markers is loaded and deployed from the delivery.
  • the absorbable radiopaque markers are used in a variety of intraluminal endoprostheses such as stents, grafts, filters, occlusive devices, and valves.
  • the endoprostheses are implanted in airways, the digestive system, and the vascular system.
  • the absorbable polymer matrix undergoes degradation and eventually disintegrates releasing the nondegradable radiopaque constituents into the body. If the endoprosthesis and markers have been fully incorporated in the vessel wall, the radiopaque substances will be contained within the local tissue (as with a stent). If the endoprosthesis and markers are not ingrown and incorporated, the radiopaque substances may be released into the body fluid.
  • the release is of little concern in the digestive system, because the small concentration of particles liberated are likely to have little affect on bile and would be quickly excreted.
  • the release of particles into the vascular system is less desirable but this can be avoided by using low loading percentages and fine particle sizes for vascular device indications.
  • the function of the absorbable threaded radiopaque marker is to indicate on a radiographic image the location of the stent within the treatment site and the length of the expanded stent can be determined by measuring the length of the marker as it follows the stent shape if the marker was threaded along a stent wire helix or axially along a line in the stent.
  • the marker can be threaded circumferentially at each end of the stent covering in a covered stent or stent-graft to indicate the location of the radiolucent covering material.
  • the stent expansion during deployment can be observed radiographically by watching the radiopaque marker helical or circumferential strand open up as the self-expanding stent is released from its radially constrained state.
  • Discrete bioabsorbable-radiopaque markers have the same functional purpose as the threaded markers, but they can be more easily used to mark the specific locations of features of interest on the stent. For example, a discrete bioabsorbable-radiopaque marker can be added to the center of the stent length to aid the physician in centering the stent within the stricture. Discrete bioabsorbable-radiopaque markers could be used to attach covering fabrics or films to stents to make stent grafts so that the location of the covering on the stent could be determined radiographically.
  • the discrete bioabsorbable-radiopaque markers can be made from biocompatible absorbable polymers containing elements with relatively high atomic numbers such as titanium, tantalum, zirconium, and platinum.
  • the radiopaque elements can be added by metallurgically alloying or by making clad composite structures. Radiopaque constituents may be filled into hollow cores, cavities or pores in the polymer matrix.
  • Organic radiopaque powders containing elements or salts or oxides of elements such as bromine, iodine, iodide, barium, and bismuth could be used instead of metal powders.
  • the amount of radiopaque constituent that is added to the absorbable polymer matrix is generally from about 1-80 weight percent, but the specific loading depends upon the atomic number of the radiopaque constituent and the thickness of the marker.
  • Metallic elements like tantalum and platinum which have high atomic numbers can be loaded in small percentages (about 1-20 weight percent) while metallic elements with lower atomic numbers such as titanium and zirconium have to be loaded in higher percentages (about 20-40%).
  • Organic radiopaque constituents with relatively low atomic numbers like iodine and bromine require loading percentages of from about 40-80 weight percent while organics with higher atomic numbers could be as low as 10% in thick markers. It is desirable to have the radiopaque constituent particle size be less than 10 microns so that when dispersed into the body the particles will not be so large as to cause obstruction or embolization.
  • An absorbable threaded radiopaque marker can be in the form of a strand of poly ( ⁇ -hydroxy acid) polymer containing radiopaque elements, oxides, or salts of elements with atomic numbers of from about 22 to about 83 interwoven or interbraided along a helical, circumferentail, or axial orientation on an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve.
  • the radiopaque material has a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • An absorbable threaded radiopaque marker can be in the form of a strand of poly ( ⁇ -hydroxy acid) polymer containing radiopaque elements, oxides, or salts of elements with atomic numbers of from about 22 to about 83 disposed on one or more surfaces of an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve.
  • the radiopaque material has a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • An absorbable threaded radiopaque marker can be in the form of a strand of poly ( ⁇ -hydroxy acid) polymer containing radiopaque elements with atomic numbers of from about 22 to about 83, loaded into hollow cores, cavities, or pores of the polymer portion and disposed on an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve.
  • the radiopaque material has a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • An absorbable threaded radiopaque can be a coated or clad composite marker strand of poly ( ⁇ -hydroxy acid) polymer and radiopaque metallic elements with atomic numbers of from about 22 to about 83, preferably titanium, tantalum, zirconium, and disposed on an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve.
  • the radiopaque material has a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • An absorbable threaded radiopaque marker can be in the form of a strand of poly ( ⁇ -hydroxy acid) polymer monofilament, ribbon, or multifilament wire containing radiopaque metallic elements with atomic numbers of from about 22 to about 83, preferably compounded or coated with titanium, tantalum, zirconium, and platinum metal powders or bromine, iodine, iodide, barium, and bismuth element, oxides or salts disposed on an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve.
  • the radiopaque material has a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • An absorbable threaded radiopaque marker can be in the form of poly ( ⁇ -hydroxy acid) polymer matrix composite strand containing radiopaque metallic elements with atomic numbers of from about 22 to about 83, preferably titanium, tantalum, zirconium, and platinum metal powders or bromine, iodine, iodide, barium, and bismuth element, oxides or salt powders disposed on an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve.
  • the radiopaque material has a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • a discrete bioabsorbable-radiopaque marker can be in the form of poly ( ⁇ -hydroxy acid) polymer containing radiopaque metallic elements with atomic numbers of from about 22 to about 83, preferably titanium, tantalum, zirconium, and platinum attached by wrapping, coiling, or tying around features within an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve such that the marker is attached and bioabsorbably removable from the endoprosthesis.
  • the radiopaque material has a linear attenuation coefficient of from about 10 cm ⁇ 1 at 50 KeV to about 120 cm ⁇ 1 at 50 KeV.
  • FIGS. 8 a - 8 c illustrating alternative embodiments of a portion of a bioabsorbable-radiopaque marker 14 .
  • the bioabsorbable-radiopaque marker 14 may have at least one portion for temporary containment of a radiopaque material.
  • the radiopaque material may be disposed in one or more hollow, cavity or pore portions in the marker 14 .
  • FIG. 8 a shows a solid bioabsorbable-radiopaque marker 14 .
  • the bioabsorbable-radiopaque marker 14 may receive a radiopaque core 13 disposed in the once hollow 15 portion.
  • the radiopaque core 13 may be slowly released from the open ends 14 a , 14 b of the hollow portion 15 into the body. Alternatively, the radiopaque core 13 may be released from the radiopaque core 13 through pores in the walls of the marker 14 into the body.
  • FIG. 9 is an illustration of a bioabsorbable-radiopaque marker 14 having pores 35 .
  • the pores may connect to a reservoir of radiopaque material in a cavity 25 or hollow 15 area or he individual pores 35 may be filled with radiopaque material.
  • the pores 35 allow the radiopaque material disposed in the marker 14 to exit from the marker 14 over a period of time.
  • the radiopaque material may be solid or include a bioabsorbable casing surrounding a liquid, solid, gel, powder, or combination thereof and be held in place in a hollow portion 15 , cavity 25 , or porous 35 portion by a relatively weak bioabsorbable adhesive, bioabsorbable gelatin, friction, or by other mechanical or chemical means known in the art.
  • the radiopaque material may be designed to disperse from the bioabsorbable-radiopaque marker 14 after a predetermined period of time.
  • the radiopaque material preferably has at least one element with an atomic number of from about 22 to about 83 and is removably-attachable in at least one hollow 15 , cavity 25 , or porous 35 portions in the marker 14 .
  • the bioabsorbable-radiopaque marker 14 may further comprise one or more walls 30 including walls between hollow 15 , cavity 25 , and porous 35 portions, proximal and distal walls, and combinations thereof that are adapted to bioabsorb in vivo.
  • FIGS. 10 a - 10 d illustrating different embodiments of the bioabsorbable-radiopaque marker 14 having hollow 15 , cavity 25 , porous 35 portions, or combinations thereof filled with a non-toxic radiopaque material.
  • FIG. 10 a shows a bioabsorbable-radiopaque marker 14 with a hollow 15 portion filled with radiopaque material and having at least one of the proximal or distal ends open
  • FIG. 10 b shows a bioabsorbable-radiopaque marker 14 with a cavity 25 portion filled with radiopaque material having closed ends
  • FIG. 10 c shows a bioabsorbable-radiopaque marker 14 with porous 35 portions filled with radiopaque material.
  • FIG. 10 d shows a bioabsorbable-radiopaque marker 14 with combinations of hollow 15 , cavity 25 , and porous 35 portions filled with radiopaque material.
  • the bioabsorbable-radiopaque marker 14 reacts with body fluids and decomposes and then the constituents are absorbed or excreted from the body.
  • FIG. 11 illustrates discrete bioabsorbable-radiopaque markers 14 made by forming small rings or coils of bioabsorbable-radiopaque filament around features of the implantable endoprosthesis 16 .
  • Relatively small and discrete filament loops (pigtail) bioabsorbable-radiopaque markers 14 are shown at the wire crossing points on the tubular braid.
  • FIG. 12 illustrates the detail bounded by the dashed-line circle in FIG. 11 showing a bioabsorbable-radiopaque marker 14 around one implantable endoprosthesis 16 wire crossing point.
  • FIG. 13 illustrates the bioabsorbable-radiopaque marker 14 of FIG. 12 and FIG. 13 and shows filament ends 14 a , 14 b which simply pass over each other to form an enclosed loop that is further preferably knotted, twisted, or tied at ends 14 a , 14 b .
  • the bioabsorbable-radiopaque markers 14 may be relatively small and comprise a single loop or pigtail of filament around one filament crossing point, filament, an embolization coil, or the like.
  • the bioabsorbable-radiopaque marker 14 is preferably made of a PGA, Polydioxanone, PLLA, PDLA, or combinations thereof.
  • Biocompatible radiopaque metal constituents preferably include titanium, zirconium, tantalum, and platinum.
  • Preferred organic radiopaque constituents include bromine, barium, bismuth, iodine, or combinations thereof.
  • the bioabsorbable-radiopaque marker 14 is preferably formed from an elongate member such as a filament and shaped accordingly onto the implantable endoprosthesis 16 .
  • the bioabsorbable-radiopaque marker 14 advantageously allows custom marking of the implantable endoprosthesis 16 without the need to acquire preformed marker bands or to devise a complicated manufacturing operation.
  • the bioabsorbable-radiopaque markers 14 may be easily and quickly added to the implantable endoprosthesis 16 . Also, only small, specific sites are marked by the bioabsorbable-radiopaque marker 14 so a minimum amount of foreign body material would be added to the implantable endoprosthesis 16 .
  • the bioabsorbable-radiopaque markers 14 should preferably be smaller than the size of the element in the implantable endoprosthesis 16 .
  • a smaller diameter bioabsorbable-radiopaque marker 14 should fit through most weaves, be deformable, and may be cut to size.
  • FIGS. 12-13 illustrating discrete bioabsorbable-radiopaque markers 14 looped one or more times about a filament or filament crossing point to prevent release therefrom.
  • the ends 14 a , 14 b are clipped and positioned to lie in a plane parallel to the longitudinal axis of the implantable endoprosthesis 16 .
  • the bioabsorbable-radiopaque marker 14 may be disposed on one or more filament crossing or every other filament crossing point around the circumference of the braid in one circular transverse plane.
  • the bioabsorbable-radiopaque markers 14 may be positioned to form one or more circumferential rings on the implantable endoprosthesis 16 .
  • the bioabsorbable-radiopaque markers 14 may be positioned along an embolization occlusion coil intravascular device or filament at predetermined locations as illustrated in FIG. 15 .
  • the ends 14 a , 14 b may then be tied, twisted, knotted, or adhesively connected together and thereafter clipped and positioned to lie in an unobtrusive low-profile position.
  • bioabsorbable-radiopaque marker 14 may be constructed using a number of methods and materials, in a wide variety of sizes and styles for the greater efficiency and convenience of a user.
  • a bioabsorbable marker that may advantageously be used in conjunction with the present invention is disclosed in J. Stinson's and Claude Clerc's U.S. patent application entitled “Radiopaque Markers And Methods Of Using Same”, Ser. No. ______ , filed concurrently herewith, and commonly assigned to the assignee of this application.
  • a bioabsorbable stent that may advantageously be used in conjunction with the present invention is disclosed in J. Stinson's U.S. patent application entitled “Bioabsorbable Implantable Endoprosthesis With Reservoir And Method Of Using Same”, Ser. No. ______; filed concurrently herewith, and commonly assigned to the assignee of this application.

Abstract

A temporary bioabsorbable-radiopaque marker for use on an implantable endoprosthesis. The bioabsorbable-radiopaque marker is adapted to be disposed on or adjacent an implantable endoprosthesis in a body lumen for a predetermined amount of time until the bioabsorbable and radiopaque materials are absorbed or dispersed in the body.

Description

    BACKGROUND OF THE INVENTION
  • This invention relates generally to a bioabsorbable marker having radiopaque constituents “bioabsorbable-radiopaque marker” for use on an implantable endoprosthesis such as a stent. The bioabsorbable marker includes dispersable radiopaque constituents which are not bioabsorbable or degradable, but are excreted from the body or stored in the body.
  • Implantable endoprostheses including stents, stent-grafts, and grafts are used in percutaneous transluminal coronary angioplasty and in other medical procedures to repair and support diseased or damaged arteries and body lumens. Grafts are implanted to cover or bridge leaks or dissections in vessels. Stent-grafts are stents which generally have a porous coating attachment. Unsupported grafts are porous tubes which are typically implanted by surgical cut-down.
  • In order to visualize the passage and placement of the implantable endoprosthesis in arteries and body lumens, many surgical procedures are performed with the aid of fluoroscopic angiography. The surgical delivery device and implantable endoprosthesis may be visualized if they are radiopaque and offer radiographic contrast relative to the body. For example, X-ray radiation may be used to visualize surgical delivery devices and deployment of the implant in the body. Also, radiographic contrast solution may be injected into the body lumen so that the lumen may be seen in the fluoroscopic image.
  • In order for the Implantable endoprosthesis to be radiopaque, it must be made from a material possessing radiographic density higher than surrounding host tissue and have sufficient thickness to affect the transmission of x-rays to produce contrast in the image. Reference is made to the clad composite stent shown in U.S. Pat. No. 5,630,840. An implantable endoprosthesis may be made of metals including tantalum, or platinum having relatively high radiographic densities. Other metals such as stainless steel, superalloys, nitinol, and titanium having lower radiographic densities may also be used. Reference is made to implantable devices shown in U.S. Pat. Nos. 4,655,771; 4,954,126; and 5,061,275.
  • An implantable polymeric endoprosthesis is generally radiolucent and does not possess sufficient radiographic density to be easily imaged by fluoroscopy. To improve the imaging of such polymeric materials, polymers may be mixed with radiopaque filler materials prior to molding or extruding in order to enhance the radiographic density. However, a disadvantage of using fillers with polymers is that changes in the properties of the polymer may occur. For example, the additions of fillers may reduce the strength or ductility of the polymer.
  • There is a need for an improved bioabsorbable-radiopaque marker for use in medical devices, particularly in temporary medical devices having low radiopacity. The need to improve the radiopacity of a relatively low radiopaque implantable endoprosthesis or to improve imaging in low radiopaque conditions is particularly important for surgery, micro-surgery, neuro-surgery, and conventional angioplasty procedures performed under fluoroscopy. Physicians are constantly being challenged to place small implants at specific intraluminal locations. Various devices having radiopacity are known in the art such as shown in U.S. Pat. Nos. 4,447,239; 5,354,257; and 5,423,849.
  • All documents cited herein, including the foregoing, are incorporated herein by reference in their entireties for all purposes.
  • SUMMARY OF THE INVENTION
  • Accordingly, there is a need for bioabsorbable-radiopaque markers for use on implantable endoprostheses in order to improve radiopacity and the locatability of an endoprosthesis during various medical procedures. Providing temporary radiopacity is especially advantageous for implantable endoprostheses having little or no radiopacity. The bioabsorbable-radiopaque markers allow radiographic identification of one or more locations of interest on an implantable endoprosthesis. Bioabsorbable-radiopaque markers in the fabric or covering materials of an implantable endoprosthesis are advantageous for indicating the location of the fabric or covering during implantation.
  • Alternative uses include threading the markers: adjacent a helical strand in the implantable endoprosthesis; circumferentially around the implantable endoprosthesis; or in a straight line in the axial direction of the implantable endoprosthesis. One or more bioabsorbable-radiopaque markers may be used on the implantable endoprosthesis having little or no radiopacity. After implantation, the bioabsorbable-radiopaque marker may be absorbed, dissolved, or excreted from the body so as not to effect the function of the endoprosthesis.
  • A disadvantage of certain permanent radiopaque markers is that they may compromise structural integrity, may not be biocompatible or biostable, and may be more thrombogenic than the implantable endoprosthesis.
  • The bioabsorbable-radiopaque marker of the present invention advantageously allows most any implantable endoprosthesis to have temporary radiopacity over a predetermined portion of its structure, and advantageously assists with proper positioning and locatability of the implantable endoprosthesis in a body lumen.
  • Use of the bioabsorbable-radiopaque marker is advantageous because the radiopaque property may be present only for a desired time period on an implantable endoprosthesis. For instance, once the implantable endoprosthesis is implanted, it may be more desirable to image with techniques such as ultrasound, magnetic resonance, and endoscopy and to avoid further radiation exposure to the patient. As the bioabsorbable polymer degrades, radiopaque material simultaneously or subsequently disperses into the body. The dispersion of the radiopaque material from the marker results in a loss of radiopacity in the marker. A predetermined rate of release of the radiopaque material may be designed into the bioabsorbable marker based on degradation of the polymer in the body or the design of the marker structure.
  • The bioabsorbable material in the bioabsorbable-radiopaque markers may include polymers or copolymers such as polylactide [poly-L-lactide (PLLA), poly-D-lactide (PDLA)], polyglycolide, polydioxanone, polycaprolactone, polygluconate, polylactic acid-polyethylene oxide copolymers, modified cellulose, collagen, poly(hydroxybutyrate), polyanhydride, polyphosphoester, poly(amino acids), poly(alpha-hydroxy acid) or related copolymers materials, each of which have a characteristic degradation rate in the body. For example, polyglycolide and polydioaxanone are relatively fast-bioabsorbing materials (weeks to months) and PLA is a relatively slow-bioabsorbing material (months to years). For a PLA member, mass degradation is completed with total absorption of the polymer endoprosthesis in about 1.5 to 3 years after implantation.
  • Bioabsorbable resins such as PLLA, PDLA, PGA and others are commerciallv available from several sources including PURAC America, Inc. of Lincolnshire, Ill. Radiopaque materials such as barium sulfate and bismuth trioxide are commerciallv available and compounded with the bioabsorbable resin by New England Urethane, Inc. of North Haven, Conn. The bioabsorbable resin or bioabsorbable-radiopaque resin may be extruded into filament by Albany International Research Co. of Mansfield, Mass.
  • The bioabsorption rate of the marker may be designed to be fast for applications where acute radiopacity is desired such as during positioning and placement of the implant. Alternatively, the bioabsorption rate may be designed to be slower for applications where the implant must be radiographically imaged for at least a portion of its functional time, for example, in implants where healing may take months. Other bioabsorption rates are also possible. The bioabsorption rate of the marker may be tailored by controlling the type of bioabsorbable polymer; chemical composition of the bioabsorbable polymer; molecular weight of the bioabsorbable polymer; thickness and density of the bioabsorbable polymer; surface area of the marker, exit area for the radiopaque material, and design of the marker structure.
  • The degradation products from the bioabsorbable marker and the dispersed radiopaque material are metabolized, excreted, or stored by the body. Metabolism is the chemical process in living cells by which energy is provided for vital processes and activities and new material is assimilated to repair the waste. It is the sum of the processes by which a particular substance is handled in the living body. Excretion is separation and elimination or discharge from the blood or tissues of useless, superfluous, or harmful material that is eliminated from the body.
  • The biocompatibility of absorbable polymers during degradation depends upon the rate of accumulation and how well the surrounding tissue or fluid buffers or metabolizes the degradation products. If the products are metabolizable, the rate at which this will occur is dependent upon the blood circulation in the tissue. A well-vascularized lumen wall could buffer and metabolize degradation products as they are released from the implant. This biological process is important to minimize adverse tissue reaction to the degrading implant.
  • The degradation products from PLLA and PGA are lactic and glycolic acid, respectively, which are normally present in the human body. The acids are metabolized by cells around the implant. The metabolization process is a citrate cycle which converts the acids to carbon dioxide which is respirated out of the body.
  • The radiopaque agents added to the bioabsorbable marker are generally insoluble in the body and thus are not metabolizable. If these materials are trapped within tissue, the host generally reacts by encapsulation and acceptance of the biologically inactive particles. If the material is released from the implant into systemic circulation, it will migrate with fluid flow until being excreted or collected and stored by organs or tissue. The idea is to only have small amounts of the radiopaque substances in the implant by incorporating the discrete bioabsorbable-radiopaque marker rather than to load the entire implant with the radiopaque material. Minimization of the amount of radiopaque material which will be liberated from the marker upon absorption of the polymer must be considered when determining the loading percentage based on radiographic and mechanical properties.
  • To be radiopaque, the markers should include material having atomic elements of sufficiently high atomic number and be of sufficient thickness to provide sufficient radiopacity for imaging. The bioabsorbable-radiopaque marker may have one or more hollow, cavity, or porous portions wherein radiopaque material may be disposed.
  • Attenuation is the change in the number of photons in the incident x-ray beam due to the interaction with an absorber. To image an object implanted in the body, it would be desirable to have the object attenuate x-rays more than body tissue, bone, and fat so that the difference in contrast will be obvious in a radiograph. The difficulty in selecting a radiopaque material for surgical implants is that the material must have desirable radiographic characteristics and biocompatibility.
  • In order to make an implant more radiopaque, a substance which absorbs more x-rays can be deposited on or mixed in with the implant material. If the implant absorbs more x-rays than the surrounding medium (for example tissue in the body), it will be visible as a sharp change in contrast on an x-ray film or fluoroscopy image.
  • The fraction of x-ray energy transmitted through the absorber is quantitatively predicted by the following equation described in The Physics of Radiology, Fourth Ed., H. Johns, J. Cunningham, 1983, pp. 137-142.
    N=N 0 e −μx
    • N=number of photons transmitted through x
    • N0=number of photons in the incident beam
    • μ=linear attenuation coefficient of the absorber
    • x=absorber thickness
  • N/N0 would be the fraction of incident x-ray energy that is transmitted through the absorber. A more radiopaque material would have a lesser fraction of transmitted energy than a more radiolucent material. Therefore, to enhance the radiopacity of a material, such as the marker material, it would be desirable to select a material with high x-ray absorbing capability to minimize the fraction of transmitted energy. This radiopacity capability is proportional to the linear attenuation coefficient and the thickness of the absorber material. The higher the attenuation coefficient of the absorber material for a given thickness, the more radiopaque the absorber will be. The attenuation produced by an absorber is dependent upon the number of electrons and atoms present in the absorber. One way of quantifying this absorption characteristic is with the atomic attenuation coefficient which is directly proportional to the linear attenuation coefficient and the atomic number of the absorber element. Radiopacity is therefore generally proportional to the atomic number (number of electrons in the atom) of the material. Candidate materials for enhancing the radiopacity of surgical implants would have higher atomic numbers than the elements present in the body and would have to be biocompatible. The atomic number must be sufficiently high so that relatively small thickness of absorber material can be used in the body. Reference is also made to linear attenuation coefficient described in U.S. Pat. No. 5,628,787. Reference is made to Table 1 which describes a number of elements and their respective atomic numbers and certain linear attenuation coefficients.
    TABLE 1
    Element or Atomic Number or Linear Attenuation Coefficient
    Material Effective Atomic Number at 50 KeV, cm−1
    hydrogen 1 .000028
    carbon 6 .417
    fat 6.46 .1925
    water 7.51 .2245
    muscle 7.64 .2330
    air 7.78 .00025
    nitrogen 7 .00023
    oxygen 8 .00028
    bone 12.31 .5727
    titanium 22
    iron 26 15.2
    cobalt 27 18.8
    bromine 35
    zirconium 40
    iodine 53 45
    barium 56 58
    tantalum 73 111
    platinum 78 108
    gold 79 101
    lead 82 88.7
    bismuth 83 108
  • The elements hydrogen, oxygen, carbon, and nitrogen are commonly found in the body and in polymers, so elements with higher atomic numbers than these should enhance the radiopacity of a polymer implant or marker. Tantalum, zirconium, titanium, barium, bismuth, and iodine are known to be non-toxic in certain concentrations and thus are candidate elements for enhancing radiopacity of a polymer marker in an implant. These elements can be added to the polymer in various loading percentages and the threshhold above which the loading causes unsatisfactory changes in the polymer characteristics can be determined through material and device testing. The elements which can be added in quantities sufficient to enhance radiopacity and maintain an acceptable level of polymer properties and which are biocompatible could be utilized in markers. The biocompatible elements with a range of atomic numbers of from about 22 to about 83 and having linear attenuation coefficients in the range of from about 10 to about 120 cm−1 at 50 KeV should provide enough enhancement in radiopacity without excessive thickness being necessary to be useful in markers. These elements would include at least titanium, vanadium, chromium, iron, cobalt, nickel, copper, bromine, zirconium, niobium, molybdenum, silver, iodine, barium, tantalum, tungsten, platinum, gold, and bismuth. The preferred metallic elements for biocompatibility and radiopacity are titanium, zirconium, tantalum, and platinum. The preferred organic elements for biocompatibility and radiopacity are bromine, iodine, barium, and bismuth. Especially preferred elements are tantalum, platinum, barium, and bismuth because of their high atomic numbers and biocompatibility (atomic numbers from 56 to 83 and linear attenuation coefficients from 30 to 120). Tantalum and platinum are used as stent components and barium sulfate and bismuth trioxide are used as radiopaque enhancements for polymer catheters.
  • The bioabsorbable-radiopaque marker may be integrated into a subassembly or a finished implantable endoprosthesis during manufacture. Radiopaque elongate elements may be braided together with non-radiopaque bioabsorbable elongate elements to form a tubular braided stent, or the bioabsorbable and radiopaque elongate elements may be woven into the finished-braided stent.
  • The bioabsorbable-radiopaque marker would advantageously add temporary radiopacity to an implantable endoprosthesis such that the temporary marker would not require a medical procedure for removal from the patient.
  • In sum the invention relates to an implantable endoprosthesis and bioabsorbable-radiopaque marker system including an implantable endoprosthesis adapted to be disposed in a body lumen and at least one marker. The marker having a proximal end, a distal end, and a thickness. The marker including bioabsorbable material and radiopaque material and is disposed on or adjacent the endoprosthesis. The marker is adapted to degrade in vivo whereby the bioabsorbable material is metabolized through or excreted from the body and the radiopaque material is excreted from or stored in the body. The bioabsorbable material may include a polymer or copolymer. The bioabsorbable material may include poly-L-lactide, poly-D-lactide, polyglycolide, polydioxanone, polycaprolactone, and polygluconate, polylactic acid-polyethylene oxide copolymers, modified cellulose, collagen, poly(hydroxybutyrate), polyanhydride, polyphosphoester, poly(amino acids), poly(alpha-hydroxy acid) and combinations thereof. The radiopaque material may have a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV. The marker may have an average thickness of from about 20 microns to about 500 microns and the radiopaque material includes at least one element with an atomic number of from about 22 to about 83. The radiopaque material may include barium sulfate, bismuth trioxide, bromine, iodine, iodide, titanium oxide, zirconium oxide, tantalum, and combinations thereof. The radiopaque material may be an oxide or salt material. One of the bioabsorbable material or radiopaque material may be coated or compounded with the other and the radiopaque material may have a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV. The marker may have a weight percent of the radiopaque material in the bioabsorbable material of from about 1% to about 80%. The bioabsorbable material may consist of PLLA and the radiopaque material may consist of bismuth trioxide and the weight percent of the bismuth trioxide in the PLLA may be at least about 10%. The bioabsorbable material may consist of PLLA and the radiopaque material may be barium sulfate and the weight percentage of the barium sulfate in the PLLA may be at least about 10%. The marker may substantially degrades in less than about 3 years. “Substantial degradadation of the marker” means that the marker has lost at least 50% of its structural strength. It is preferable that the marker lose about 100% of its structural strength. The bioabsorbable material may consist of polylactide and the radiopaque material may consist of barium sulfate, bismuth trioxide, iodine, iodide, and combinations thereof and the marker substantially degrades in from about 1 year to about 2 years. The bioabsorbable material may include poly-L-lactide, poly-D-lactide, polyglycolide, and combinations thereof and the radiopaque material may include barium sulfate, bismuth trioxide, bromine, iodine, iodide, and combinations thereof and the marker substantially degrades in from about 3 months to about 1 year. The bioabsorbable material may include polyglycolide, polygluconate, polydioxanone, and combinations thereof and the radiopaque material may include barium sulfate, bismuth trioxide, bromine, iodine, iodide, and combinations thereof and the marker substantially degrades in from about 1 week to about 3 months. The marker may be a mono-filament, multi-filament, thread, ribbon, suture, and combinations thereof. The marker may include one or more hollow, cavity, porous, and combinations thereof portions and the radiopaque material may be disposed therein. The marker may have radiopacity for a predetermined amount of time. The endoprosthesis may be a stent, stent-graft, graft, filter, occlusive device, or valve. The endoprosthesis may have a tubular, radially expandable structure and axially flexible structure including a plurality of the elongate elements which are interwoven in a braid-like configuration.
  • The invention also relates to an implantable endoprosthesis and bioabsorbable-radiopaque marker system including an implantable endoprosthesis adapted to be disposed in a body lumen and at least one elongated marker. The marker is adapted to be disposed on or adjacent the endoprosthesis. The marker includes a proximal end, distal end, thickness, bioabsorbable material, and a radiopaque material having a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV. The marker has at least one hollow, cavity, or porous portion where the radiopaque material may be disposed. The bioabsorbable material at least partially contains the radiopaque material in the marker. The radiopaque material may be a liquid, solid, powder, gel, particle, or combinations thereof.
  • The invention also relates to a method of marking an implantable endoprosthesis including: disposing at least one elongate marker on or adjacent to at least a portion of an implantable endoprosthesis. The marker is from about 20 weight percent to about 99 weight percent of a bioabsorbable polymer and from about 1 weight percent to about 80 weight percent of a radiopaque material. The radiopaque material includes liquid or particles, the particles having an average diameter less than about 200 microns and a maximum diameter less than about 400 microns. The radiopaque material has a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV; disposing the endoprosthesis and marker in a delivery system; inserting the delivery system in a body lumen; deploying the endoprosthesis and marker from the delivery system into a body lumen; and allowing the polymer to bioabsorb or excrete and the radiopaque material to subsequently or simultaneously at least partially disperses from the endoprosthesis.
  • The invention also relates to a temporary bioabsorbable-radiopaque marker including a marker having an average thickness less than about 500 microns and consisting of a bioabsorbable material and a radiopaque material, the radiopaque material having a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV. The marker is adapted to be disposed in a body lumen and degrade in vivo. The marker may be elongate and have a proximal end and a distal end.
  • The invention also relates to a bioabsorbable-radiopaque marker including an elongate element adapted to be disposed in a body lumen and used as a surgical guide, the element including a bioabsorbable material, a radiopaque material, and combinations thereof. The element has a weight percent, W, of the radiopaque material in the bioabsorbable material, and an average thickness, T, over the length of the elongate element. The weight percent, W, is equal to about:
      • (i) [10+((950×T(measured in mm))−208.5)]±5 for radiopaque material having atomic weight 20-100;
      • (ii) ((950×T(measured in mm))−208.5)±5 for radiopaque material having atomic weight of 100 to 150 up to a maximum of 80 weight percentage; or
      • (iii) [((950×T(measured in mm))−208.5)−10]±5 for radiopaque material having atomic weight greater than 150. The minimum W is about 1 and the maximum W is about 80.
  • The invention also relates to a marker including from about 20 weight percent to about 99 weight percent of a bioabsorbable polymer; and from about 1 weight percent to about 80 weight percent of a radiopaque material. The radiopaque material includes at least one of a liquid or particle having an average particle diameter less than about 8 microns and a maximum particle diameter less than about 10 microns. The radiopaque material has a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV. For vascular system. The preferred average particle size is from about 3 microns to about 6 microns and a maximum particle size of 6 microns. For the digestive system, the average particle size may be from about 100 microns to about 150 microns and a maximum particle size of 400 microns.
  • Still other objects and advantages of the present invention and methods of construction of the same will become readily apparent to those skilled in the art from the following detailed description, wherein only the preferred embodiments are shown and described, simply by way of illustration of the best mode contemplated of carrying out the invention. As will be realized, the invention is capable of other and different embodiments and methods of construction, and its several details are capable of modification in various obvious respects, all without departing from the invention. Accordingly, the drawing and description are to be regarded as illustrative in nature, and not as restrictive.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1 is a side view of stent delivery system having a bioabsorbable-radiopaque marker disposed on an implantable endoprosthesis;
  • FIG. 2 is a side view of the delivery system and a deployed implantable endoprosthesis in a body lumen;
  • FIGS. 3 a, 3 b, and 3 c are cross-sectional views of three alternative marker dispositions of the bioabsorbable-radiopaque marker on the implantable endoprosthesis at section 3-3 of FIG. 2;
  • FIG. 4 is a side view of a bioabsorbable-radiopaque marker disposed in a longitudinal pattern on a implantable endoprosthesis;
  • FIG. 5 is a side view of a bioabsorbable-radiopaque marker disposed in a helical pattern on a implantable endoprosthesis;
  • FIG. 6 is a side view of a relatively flexible bioabsorbable-radiopaque marker;
  • FIGS. 7 a-7 e are cross-sectional views of five alternative bioabsorbable-radiopaque markers at section 7-7 of FIG. 6;
  • FIGS. 8 a-8 c are side views of three alternative bioabsorbable-radiopaque markers;
  • FIG. 9 is a side views of a porous bioabsorbable-radiopaque marker; and
  • FIGS. 10 a-10 d are side views of four elongate elements having radiopaque materials therein.
  • FIG. 11 is a side view illustrating one possible arrangement of discrete bioabsorbable-radiopaque markers disposed on an implantable endoprosthesis;
  • FIG. 12 is the detail bounded by the dashed-line circle in FIG. 12 illustrating a bioabsorbable-radiopaque marker disposed around one implantable endoprosthesis wire crossing point;
  • FIG. 13 is a side view illustrating a discrete radiopaque marker; and
  • FIG. 14 illustrates the discrete bioabsorbable-radiopaque marker positioned on an embolization occlusion coil intravascular device.
  • DETAILED DESCRIPTION OF THE INVENTION
  • Reference is made to FIG. 1 illustrating a stent delivery device 10 having one or more bioabsorbable-radiopaque markers 14 disposed in a helical pattern on an implantable endoprosthesis 16. The bioabsorbable-radiopaque marker 14 is disposed on the endoprosthesis 16 preferably before loading the assembly thereof into the outer tube of a delivery device 10. Reference is made to a delivery device shown in U.S. Pat. No. 5,026,377.
  • FIG. 2 illustrates an implantable endoprosthesis 16 having a bioabsorbable-radiopaque markers 14 disposed in a helical pattern thereon in a body lumen 12. Implantable endoprostheses 16 known in the art include stents, stent-grafts, grafts, filters, occlusive devices, valves, and combinations thereof, all may incorporate the bioabsorbable-radiopaque marker 14.
  • FIGS. 3 a-3 c illustrate three alternative locations on an implantable endoprosthesis 16 for disposing the bioabsorbable-radiopaque marker. The bioabsorbable-radiopaque marker 14 may be disposed on portions of the inside surface 17, outside surface 19, or be inter-woven or inter-braided about and through the elongated elements of the implantable endoprosthesis 16. The bioabsorbable-radiopaque marker 14 may be disposed on the implantable endoprosthesis 16 in one or more predetermined lengths.
  • Reference is made to FIGS. 4 and 5 illustrating the bioabsorbable-radiopaque marker 14 disposed in two alternative patterns on the implantable endoprosthesis 16. FIG. 4 shows the bioabsorbable-radiopaque marker 14 interwoven through the filaments of the endoprosthesis 16 in a relatively longitudinal pattern. Alternatively, the bioabsorbable-radiopaque marker 14 may be interwoven through the filaments of the endoprosthesis 16 in a relatively circumferential pattern. FIG. 5 shows a marker 14 interwoven through the filaments of the endoprosthesis 16 in a relatively helical pattern. Other patterns and dispositions of the bioabsorbable-radiopaque marker 14 on the endoprosthesis 16 are also possible. One or more markers 14 may be temporarily disposed on the implantable endoprosthesis 16 to advantageously provide temporary radiopacity to predetermined locations on the implantable endoprosthesis 16.
  • As shown in FIGS. 3 a and 3 c, the bioabsorbable-radiopaque marker 14 may be disposed to one or more surfaces of the implantable endoprosthesis 16 with a relatively weak bioabsorbable adhesive or gelatin.
  • The bioabsorbable-radiopaque marker 14 may include elongate elements such as a ribbon, thread, filament, suture, or combinations thereof. The bioabsorbable-radiopaque marker 14 may be braided to form a rope or cable.
  • As the implantable endoprosthesis 16 is deployed from the delivery device 10, the bioabsorbable-radiopaque marker 14 may adjust with the expansion of the implantable endoprosthesis 16, and advantageously provide radiopacity and enhance the viewing of the implantable endoprosthesis 16 position or size during fluoroscopy. Once the implantable endoprosthesis 16 is fully deployed, the delivery device 10 may be removed from the body and the bioabsorbable-radiopaque marker 14 may remain on the implantable endoprosthesis 16 to be bioabsorbed, dissolved, dispersed, or excreted from the body. The bioabsorbable-radiopaque marker 14 may be designed to remain on the implantable endoprosthesis 16 for a predetermined period of time if there is a need for follow-up angiography.
  • Reference is made to FIG. 6 illustrating a bioabsorbable-radiopaque marker 14 preferably made from a relatively flexible elongate polymeric material including radiopaque material containing at least one element with an atomic number of from about 22 to about 83. The radiopaque material preferably has a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV.
  • FIGS. 7 a-7 e illustrate alternative cross-sectional embodiments of the bioabsorbable-radiopaque marker 14 taken through the line 7-7 of FIG. 6. FIG. 7 a shows a substantially solid member; FIG. 7 b shows a hollow member; FIG. 7 c shows a member having pores extending radially into the member; FIG. 7 d shows a rectangular or ribbon member; and FIG. 7 e shows a braided hollow member. FIG. 7 e may also be a substantially solid braided member.
  • A composite bioabsorbable-radiopaque marker 14 may include a bioabsorbable polymer that is coated, compounded, filled, loaded, or mixed with a radiopaque substance such as iodide, iodine, zirconium oxide, barium sulfate, bismuth trioxide, or a related oxide or salt substance. Composite radiopaque materials may contain at least one element having an atomic number, preferably, higher than about 22. Other radiopaque materials may include gold, platinum, tantalum, metallic biomaterial alloys for coating, and small particles of these materials, preferably, less than 10 microns in size for compounding. For compounding radiopaque constituents and bioabsorbable resins to make extruded bioabsorbable-radiopaque filament, the weight percentage of radiopaque resins to bioabsorbable resins ranges from about 1 percent to about 80 percent. For compounding radiopaque metallic fillers and bioabsorbable resins to make extruded bioabsorbable-radiopaque filament, the weight percentage of radiopaque metallic fillers to bioabsorbable resins ranges from about 1 percent to about 40 percent. The preferred weight percentage of bismuth trioxide and barium sulfate in PLLA filament is a minimum of about 10%. Preferred embodiments of the bioabsorbable-radiopaque marker are set forth below in Table 2.
    TABLE 2
    Metal Organic Preferred Preferred
    Preferred Radiopaque Preferred Radiopaque Marker Matrix Marker Matrix
    Marker Metal Constituent Marker Organic Constituent Materials For Materials For
    Radiopaque Loading, Radiopaque Loading, Fast Slow
    Marker Type Function Devices Constituents Weight % Constituent Weight % Absorption Absorption
    threading on mark overall braided tubular Ti, Ta, Zr, Pt Ti, Zr = 15-40 Br, I, Ba, Bi Br, I = 40-80 PGA, PLLA, PDLA
    helix stent length, stents, filters, Ta, Pt = 1-20 Bi, Ba = 10-80 polydioxanone
    location in occlusion,
    vessel valves
    threading mark stent braided tubular Ti, Ta, Zr, Pt Ti, Zr = 15-40 Br, I, Ba, Bi Br, I = 40-80 PGA, PLLA, PDLA
    around ends, location stents, filters, Ta, Pt = 1-20 Bi, Ba = 10-80 polydioxanone
    circum- in vessel, occlusion,
    ference covering valves, stent
    length, grafts
    expansion
    threading on mark overall braided tubular Ti, Ta, Zr, Pt Ti, Zr = 15-40 Br, I, Ba, Bi Br, I = 40-80 PGA, PLLA, PDLA
    straight axial stent length, stents, filters, Ta, Pt = 1-20 Bi, Ba = 10-80 polydioxanone
    line location in occlusion,
    vessel valves, stent
    grafts
    pigtail rings mark stent braided tubular Ti, Ta, Zr, Pt Ti, Zr = 15-40 Br, I, Ba, Bi Br, I = 40-80 PGA, PLLA, PDLA
    ends or center, stents, filters, Ta, Pt = 1-20 Bi, Ba = 10-80 polydioxanone
    location in occlusion,
    vessel, valves, stent
    expansion grafts
    coils mark stent braided tubular Ti, Ta, Zr, Pt Ti, Zr = 15-40 Br, I, Ba, Bi Br, I = 40-80 PGA, PLLA, PDLA
    ends or center, stents, filters, Ta, Pt = 1-20 Bi, Ba = 10-80 polydioxanone
    location in occlusion,
    vessel, valves, stent
    expansion grafts
    knots mark stent braided tubular Ti, Ta, Zr, Pt Ti, Zr = 15-40 Br, I, Ba, Bi Br, I = 40-80 PGA, PLLA, PDLA
    ends or center, stents, filters, Ta, Pt = 1-20 Bi, Ba = 10-80 polydioxanone
    location in occlusion,
    vessel, valves, stent
    expansion grafts
  • The column for marker type in Table 2 contains a description of the physical aspects of the marker such as a strand threaded in and out of the braided stent interstices, following a wire helix or in and out of the braided stent interstices around the circumference, or in and out of the braided stent interstices in a straight line in the axial orientation. An interstice is the location where two stent wires in the braid cross over one another. The function of the marker is described in Table 2 to indicate how the marker is used in the endoprosthesis, for example, to indicate the ends of a stent or to allow radiographic visualization of the stent changing from a constrained condition to an expanded condition as it is deployed. A list of devices where the marker could be incorporated is provided in Table 2 and generally contains various types of intraluminal endoprostheses. The preferred metal radiopaque constituents (Ta, Pt, Zr, Ti) are known to be biocompatible and have relatively high atomic numbers and linear attenuation coefficients. These elements would be added to the bioabsorbable polymer to make the material radiopaque and suitable for radiographic marking. The adjacent column, Metal Radiopaque Constituent Loading, Weight %, indicates the preferred range of loading of the metal radiopaque constituents into the bioabsorbable polymer to make it sufficiently radiopaque, such as from about 1 to about 20 weight percent tantalum or platinum compounded or coated onto the polymer. The same type of information is given in the next two columns for organic radiopaque constituents. The marker may be made with either metal or organic constituents, with metal being preferred for thin markers and organics being more appropriate for thicker markers where higher loadings can be tolerated (so as to not weaken the marker significantly). The last two columns in the table contain preferred absorbable polymers for the marker matrix material. PLLA and PDLA are preferred for slow-absorbing markers, because the degradation rate of these polymers is rather slow (months to years). PGA and polydioxanone are preferred for fast-absorbing markers because the degradation rate of these polymers is rather fast (weeks to months).
  • For description purposes, the markers of the invention can be segregated into types; threaded and discrete bioabsorbable-radiopaque markers. A threaded marker is generally a strand or strands of material having radiopacity which is incorporated within the implantable device by interweaving or interbraiding the strand through the struts or wires of the endoprosthesis. A discrete bioabsorbable-radiopaque marker is generally a bioabsorbable-radiopaque polymer strand of material which is securely attached to a localized region of the implantable device and does not significantly extend over a large portion of the device.
  • An example of a threaded marker in a braided wire tubular stent is a bioabsorbable-radiopaque polymer strand loaded with a radiopaque constituent that is woven in and out of the wire crossing points following the helical path of one individual wire strand in the stent.
  • An example of a discrete bioabsorbable-radiopaque marker is a coil, knot, or ring of a bioabsorbable-radiopaque polymer strand around a feature of a stent, such as a stent wire crossing point. The strand is wrapped, coiled, or tied around the stent wire and thereby is mechanically attached to the device. The strand ends are clipped off such that the marker is present as a small, tight ring around a feature of the stent. The stent with the attached markers is loaded and deployed from the delivery.
  • The absorbable radiopaque markers are used in a variety of intraluminal endoprostheses such as stents, grafts, filters, occlusive devices, and valves. The endoprostheses are implanted in airways, the digestive system, and the vascular system. When the markers are implanted and exposed to body fluids the absorbable polymer matrix undergoes degradation and eventually disintegrates releasing the nondegradable radiopaque constituents into the body. If the endoprosthesis and markers have been fully incorporated in the vessel wall, the radiopaque substances will be contained within the local tissue (as with a stent). If the endoprosthesis and markers are not ingrown and incorporated, the radiopaque substances may be released into the body fluid. The release is of little concern in the digestive system, because the small concentration of particles liberated are likely to have little affect on bile and would be quickly excreted. The release of particles into the vascular system is less desirable but this can be avoided by using low loading percentages and fine particle sizes for vascular device indications.
  • The function of the absorbable threaded radiopaque marker is to indicate on a radiographic image the location of the stent within the treatment site and the length of the expanded stent can be determined by measuring the length of the marker as it follows the stent shape if the marker was threaded along a stent wire helix or axially along a line in the stent. The marker can be threaded circumferentially at each end of the stent covering in a covered stent or stent-graft to indicate the location of the radiolucent covering material. The stent expansion during deployment can be observed radiographically by watching the radiopaque marker helical or circumferential strand open up as the self-expanding stent is released from its radially constrained state.
  • Discrete bioabsorbable-radiopaque markers have the same functional purpose as the threaded markers, but they can be more easily used to mark the specific locations of features of interest on the stent. For example, a discrete bioabsorbable-radiopaque marker can be added to the center of the stent length to aid the physician in centering the stent within the stricture. Discrete bioabsorbable-radiopaque markers could be used to attach covering fabrics or films to stents to make stent grafts so that the location of the covering on the stent could be determined radiographically.
  • The discrete bioabsorbable-radiopaque markers can be made from biocompatible absorbable polymers containing elements with relatively high atomic numbers such as titanium, tantalum, zirconium, and platinum. The radiopaque elements can be added by metallurgically alloying or by making clad composite structures. Radiopaque constituents may be filled into hollow cores, cavities or pores in the polymer matrix. Organic radiopaque powders containing elements or salts or oxides of elements such as bromine, iodine, iodide, barium, and bismuth could be used instead of metal powders.
  • The amount of radiopaque constituent that is added to the absorbable polymer matrix is generally from about 1-80 weight percent, but the specific loading depends upon the atomic number of the radiopaque constituent and the thickness of the marker. Metallic elements like tantalum and platinum which have high atomic numbers can be loaded in small percentages (about 1-20 weight percent) while metallic elements with lower atomic numbers such as titanium and zirconium have to be loaded in higher percentages (about 20-40%). Organic radiopaque constituents with relatively low atomic numbers like iodine and bromine require loading percentages of from about 40-80 weight percent while organics with higher atomic numbers could be as low as 10% in thick markers. It is desirable to have the radiopaque constituent particle size be less than 10 microns so that when dispersed into the body the particles will not be so large as to cause obstruction or embolization.
  • EXAMPLE 1
  • An absorbable threaded radiopaque marker can be in the form of a strand of poly (α-hydroxy acid) polymer containing radiopaque elements, oxides, or salts of elements with atomic numbers of from about 22 to about 83 interwoven or interbraided along a helical, circumferentail, or axial orientation on an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve. The radiopaque material has a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV.
  • EXAMPLE 2
  • An absorbable threaded radiopaque marker can be in the form of a strand of poly (α-hydroxy acid) polymer containing radiopaque elements, oxides, or salts of elements with atomic numbers of from about 22 to about 83 disposed on one or more surfaces of an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve. The radiopaque material has a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV.
  • EXAMPLE 3
  • An absorbable threaded radiopaque marker can be in the form of a strand of poly (α-hydroxy acid) polymer containing radiopaque elements with atomic numbers of from about 22 to about 83, loaded into hollow cores, cavities, or pores of the polymer portion and disposed on an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve. The radiopaque material has a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV.
  • EXAMPLE 4
  • An absorbable threaded radiopaque can be a coated or clad composite marker strand of poly (α-hydroxy acid) polymer and radiopaque metallic elements with atomic numbers of from about 22 to about 83, preferably titanium, tantalum, zirconium, and disposed on an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve. The radiopaque material has a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV.
  • EXAMPLE 5
  • An absorbable threaded radiopaque marker can be in the form of a strand of poly (α-hydroxy acid) polymer monofilament, ribbon, or multifilament wire containing radiopaque metallic elements with atomic numbers of from about 22 to about 83, preferably compounded or coated with titanium, tantalum, zirconium, and platinum metal powders or bromine, iodine, iodide, barium, and bismuth element, oxides or salts disposed on an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve. The radiopaque material has a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV.
  • EXAMPLE 6
  • An absorbable threaded radiopaque marker can be in the form of poly (α-hydroxy acid) polymer matrix composite strand containing radiopaque metallic elements with atomic numbers of from about 22 to about 83, preferably titanium, tantalum, zirconium, and platinum metal powders or bromine, iodine, iodide, barium, and bismuth element, oxides or salt powders disposed on an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve. The radiopaque material has a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV.
  • EXAMPLE 7
  • A discrete bioabsorbable-radiopaque marker can be in the form of poly (α-hydroxy acid) polymer containing radiopaque metallic elements with atomic numbers of from about 22 to about 83, preferably titanium, tantalum, zirconium, and platinum attached by wrapping, coiling, or tying around features within an endoprosthesis such as a stent, stent-graft, graft, filter, occlusive device, and valve such that the marker is attached and bioabsorbably removable from the endoprosthesis. The radiopaque material has a linear attenuation coefficient of from about 10 cm−1 at 50 KeV to about 120 cm−1 at 50 KeV.
  • Reference is made to FIGS. 8 a-8 c illustrating alternative embodiments of a portion of a bioabsorbable-radiopaque marker 14. The bioabsorbable-radiopaque marker 14 may have at least one portion for temporary containment of a radiopaque material. The radiopaque material may be disposed in one or more hollow, cavity or pore portions in the marker 14. For example. FIG. 8 a shows a solid bioabsorbable-radiopaque marker 14. As shown in FIGS. 8 b-8 c, the bioabsorbable-radiopaque marker 14, may receive a radiopaque core 13 disposed in the once hollow 15 portion. The radiopaque core 13 may be slowly released from the open ends 14 a, 14 b of the hollow portion 15 into the body. Alternatively, the radiopaque core 13 may be released from the radiopaque core 13 through pores in the walls of the marker 14 into the body.
  • FIG. 9 is an illustration of a bioabsorbable-radiopaque marker 14 having pores 35. The pores may connect to a reservoir of radiopaque material in a cavity 25 or hollow 15 area or he individual pores 35 may be filled with radiopaque material. The pores 35 allow the radiopaque material disposed in the marker 14 to exit from the marker 14 over a period of time.
  • The radiopaque material may be solid or include a bioabsorbable casing surrounding a liquid, solid, gel, powder, or combination thereof and be held in place in a hollow portion 15, cavity 25, or porous 35 portion by a relatively weak bioabsorbable adhesive, bioabsorbable gelatin, friction, or by other mechanical or chemical means known in the art. The radiopaque material may be designed to disperse from the bioabsorbable-radiopaque marker 14 after a predetermined period of time. The radiopaque material preferably has at least one element with an atomic number of from about 22 to about 83 and is removably-attachable in at least one hollow 15, cavity 25, or porous 35 portions in the marker 14. The bioabsorbable-radiopaque marker 14 may further comprise one or more walls 30 including walls between hollow 15, cavity 25, and porous 35 portions, proximal and distal walls, and combinations thereof that are adapted to bioabsorb in vivo.
  • Reference is made to FIGS. 10 a-10 d illustrating different embodiments of the bioabsorbable-radiopaque marker 14 having hollow 15, cavity 25, porous 35 portions, or combinations thereof filled with a non-toxic radiopaque material. FIG. 10 a shows a bioabsorbable-radiopaque marker 14 with a hollow 15 portion filled with radiopaque material and having at least one of the proximal or distal ends open; FIG. 10 b shows a bioabsorbable-radiopaque marker 14 with a cavity 25 portion filled with radiopaque material having closed ends; FIG. 10 c shows a bioabsorbable-radiopaque marker 14 with porous 35 portions filled with radiopaque material; and FIG. 10 d shows a bioabsorbable-radiopaque marker 14 with combinations of hollow 15, cavity 25, and porous 35 portions filled with radiopaque material. The bioabsorbable-radiopaque marker 14 reacts with body fluids and decomposes and then the constituents are absorbed or excreted from the body.
  • FIG. 11 illustrates discrete bioabsorbable-radiopaque markers 14 made by forming small rings or coils of bioabsorbable-radiopaque filament around features of the implantable endoprosthesis 16. Relatively small and discrete filament loops (pigtail) bioabsorbable-radiopaque markers 14 are shown at the wire crossing points on the tubular braid.
  • FIG. 12 illustrates the detail bounded by the dashed-line circle in FIG. 11 showing a bioabsorbable-radiopaque marker 14 around one implantable endoprosthesis 16 wire crossing point.
  • FIG. 13 illustrates the bioabsorbable-radiopaque marker 14 of FIG. 12 and FIG. 13 and shows filament ends 14 a, 14 b which simply pass over each other to form an enclosed loop that is further preferably knotted, twisted, or tied at ends 14 a, 14 b. The bioabsorbable-radiopaque markers 14 may be relatively small and comprise a single loop or pigtail of filament around one filament crossing point, filament, an embolization coil, or the like. The bioabsorbable-radiopaque marker 14 is preferably made of a PGA, Polydioxanone, PLLA, PDLA, or combinations thereof. Biocompatible radiopaque metal constituents preferably include titanium, zirconium, tantalum, and platinum. Preferred organic radiopaque constituents include bromine, barium, bismuth, iodine, or combinations thereof.
  • The bioabsorbable-radiopaque marker 14 is preferably formed from an elongate member such as a filament and shaped accordingly onto the implantable endoprosthesis 16. The bioabsorbable-radiopaque marker 14 advantageously allows custom marking of the implantable endoprosthesis 16 without the need to acquire preformed marker bands or to devise a complicated manufacturing operation. The bioabsorbable-radiopaque markers 14 may be easily and quickly added to the implantable endoprosthesis 16. Also, only small, specific sites are marked by the bioabsorbable-radiopaque marker 14 so a minimum amount of foreign body material would be added to the implantable endoprosthesis 16.
  • The bioabsorbable-radiopaque markers 14 should preferably be smaller than the size of the element in the implantable endoprosthesis 16. A smaller diameter bioabsorbable-radiopaque marker 14 should fit through most weaves, be deformable, and may be cut to size.
  • Reference is made to FIGS. 12-13 illustrating discrete bioabsorbable-radiopaque markers 14 looped one or more times about a filament or filament crossing point to prevent release therefrom. The ends 14 a, 14 b are clipped and positioned to lie in a plane parallel to the longitudinal axis of the implantable endoprosthesis 16. The bioabsorbable-radiopaque marker 14 may be disposed on one or more filament crossing or every other filament crossing point around the circumference of the braid in one circular transverse plane. The bioabsorbable-radiopaque markers 14 may be positioned to form one or more circumferential rings on the implantable endoprosthesis 16. Alternatively, the bioabsorbable-radiopaque markers 14 may be positioned along an embolization occlusion coil intravascular device or filament at predetermined locations as illustrated in FIG. 15. The ends 14 a, 14 b may then be tied, twisted, knotted, or adhesively connected together and thereafter clipped and positioned to lie in an unobtrusive low-profile position.
  • It will be evident from considerations of the foregoing that the bioabsorbable-radiopaque marker 14 may be constructed using a number of methods and materials, in a wide variety of sizes and styles for the greater efficiency and convenience of a user.
  • A bioabsorbable marker that may advantageously be used in conjunction with the present invention is disclosed in J. Stinson's and Claude Clerc's U.S. patent application entitled “Radiopaque Markers And Methods Of Using Same”, Ser. No. ______ , filed concurrently herewith, and commonly assigned to the assignee of this application.
  • A bioabsorbable stent that may advantageously be used in conjunction with the present invention is disclosed in J. Stinson's U.S. patent application entitled “Bioabsorbable Implantable Endoprosthesis With Reservoir And Method Of Using Same”, Ser. No. ______; filed concurrently herewith, and commonly assigned to the assignee of this application.
  • Another bioabsorbable stent that may advantageously be used in conjunction with the present invention is disclosed in J. Stinson's U.S. patent application entitled “Bioabsorbable Self-Expanding Stent”, Ser. No. ______, filed concurrently herewith, and commonly assigned to the assignee of this application.
  • The above described embodiments of the invention are merely descriptive of its principles and are not to be considered limiting. Further modifications of the invention herein disclosed will occur to those skilled in the respective arts and all such modifications are deemed to be within the scope of the invention as defined by the following claims.

Claims (30)

1-46. (canceled)
47. A method, comprising:
imaging a medical device with X-rays, the medical device having a first radiopacity; and
imaging the medical device with a magnetic field, the medical device having a second radiopacity less than the first radiopacity.
48. The method of claim 47, wherein the medical device comprises a biodegradable composition.
49. The method of claim 48, wherein the biodegradable composition is in the form of a coating.
50. The method of claim 47, wherein the medical device is imaged with the magnetic field after imaging the medical device with X-rays.
51. The method of claim 47, further comprising implanting the medical device.
52. The method of claim 51, wherein the medical device is imaged with the magnetic field after implanting the medical device.
53. The method of claim 47, wherein the medical device comprises an endoprosthesis.
54. The method of claim 53, wherein the medical device comprises a stent.
55. The method of claim 53, wherein the endoprosthesis comprises a polymer.
56. The method of claim 47, wherein the medical device comprises an occlusive device.
57. A method, comprising:
imaging a medical device with a first imaging technique;
changing the visibility of the medical device, as imaged by the first imaging technique; and
imaging the medical device with a second imaging technique different than the first imaging technique.
58. The method of claim 57, wherein the first imaging technique comprises applying X-rays.
59. The method of claim 57, wherein the second imaging technique is selected from the group consisting of ultrasound, magnetic resonance, and endoscopy.
60. The method of claim 57, wherein the medical device comprises a biodegradable composition.
61. The method of claim 60, wherein the biodegradable composition is in the form of a coating.
62. The method of claim 57, wherein the medical device is imaged with the second imaging technique after imaging the medical device with the first technique.
63. The method of claim 57, further comprising implanting the medical device.
64. The method of claim 63, wherein the medical device is imaged with the second technique after implanting the medical device.
65. The method of claim 57, wherein the medical device comprises an endoprosthesis.
66. The method of claim 65, wherein the medical device comprises a stent.
67. The method of claim 65, wherein the endoprosthesis comprises a polymer.
68. The method of claim 57, wherein the medical device comprises an occlusive device.
69. An implantable medical device, comprising a radiopaque composition capable of diminishing in radiopacity after the device has been implanted in a body.
70. The device of claim 69, wherein the composition is biodegradable.
71. The device of claim 70, wherein the composition is in the form of a coating.
72. The device of claim 69, wherein the medical device comprises an endoprosthesis.
73. The device of claim 72, wherein the medical device comprises a stent.
74. The device of claim 72, wherein the endoprosthesis comprises a polymer.
75. The device of claim 69, wherein the medical device comprises an occlusive device.
US10/978,231 1997-08-01 2004-10-29 Bioabsorbable marker having radiopaque constituents and method of using the same Abandoned US20060004440A1 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
US10/978,231 US20060004440A1 (en) 1997-08-01 2004-10-29 Bioabsorbable marker having radiopaque constituents and method of using the same
US12/485,682 US20090259125A1 (en) 1997-08-01 2009-06-16 Bioabsorbable Marker Having Radiopaque Constituents And Method of Using the Same

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US08/904,951 US6174330B1 (en) 1997-08-01 1997-08-01 Bioabsorbable marker having radiopaque constituents
US09/748,474 US6626936B2 (en) 1997-08-01 2000-12-26 Bioabsorbable marker having radiopaque constituents
US10/635,114 US7553325B2 (en) 1997-08-01 2003-08-06 Bioabsorbable marker having radiopaque constituents
US10/978,231 US20060004440A1 (en) 1997-08-01 2004-10-29 Bioabsorbable marker having radiopaque constituents and method of using the same

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US10/635,114 Continuation US7553325B2 (en) 1997-08-01 2003-08-06 Bioabsorbable marker having radiopaque constituents

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US12/485,682 Continuation US20090259125A1 (en) 1997-08-01 2009-06-16 Bioabsorbable Marker Having Radiopaque Constituents And Method of Using the Same

Publications (1)

Publication Number Publication Date
US20060004440A1 true US20060004440A1 (en) 2006-01-05

Family

ID=25420033

Family Applications (5)

Application Number Title Priority Date Filing Date
US08/904,951 Expired - Lifetime US6174330B1 (en) 1997-08-01 1997-08-01 Bioabsorbable marker having radiopaque constituents
US09/748,474 Expired - Lifetime US6626936B2 (en) 1997-08-01 2000-12-26 Bioabsorbable marker having radiopaque constituents
US10/635,114 Expired - Fee Related US7553325B2 (en) 1997-08-01 2003-08-06 Bioabsorbable marker having radiopaque constituents
US10/978,231 Abandoned US20060004440A1 (en) 1997-08-01 2004-10-29 Bioabsorbable marker having radiopaque constituents and method of using the same
US12/485,682 Abandoned US20090259125A1 (en) 1997-08-01 2009-06-16 Bioabsorbable Marker Having Radiopaque Constituents And Method of Using the Same

Family Applications Before (3)

Application Number Title Priority Date Filing Date
US08/904,951 Expired - Lifetime US6174330B1 (en) 1997-08-01 1997-08-01 Bioabsorbable marker having radiopaque constituents
US09/748,474 Expired - Lifetime US6626936B2 (en) 1997-08-01 2000-12-26 Bioabsorbable marker having radiopaque constituents
US10/635,114 Expired - Fee Related US7553325B2 (en) 1997-08-01 2003-08-06 Bioabsorbable marker having radiopaque constituents

Family Applications After (1)

Application Number Title Priority Date Filing Date
US12/485,682 Abandoned US20090259125A1 (en) 1997-08-01 2009-06-16 Bioabsorbable Marker Having Radiopaque Constituents And Method of Using the Same

Country Status (7)

Country Link
US (5) US6174330B1 (en)
EP (1) EP0894503B2 (en)
JP (1) JP4284427B2 (en)
AT (1) ATE348638T1 (en)
CA (1) CA2238784C (en)
DE (1) DE69836656T3 (en)
ES (1) ES2274556T3 (en)

Cited By (46)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040249436A1 (en) * 2000-05-19 2004-12-09 Aznoian Harold M. Stents and stenting methods
US20080097401A1 (en) * 2006-09-22 2008-04-24 Trapp Benjamin M Cerebral vasculature device
WO2008084286A2 (en) * 2006-10-25 2008-07-17 Arterial Remodeling Technologies, S.A. Method for expansion and deployment of polymeric structures including stents
US20080221670A1 (en) * 2007-03-07 2008-09-11 Claude Clerc Radiopaque polymeric stent
US20090192587A1 (en) * 2005-10-03 2009-07-30 Cardiatis S.A. Radio-opaque endoprosthesis
US20090259125A1 (en) * 1997-08-01 2009-10-15 Boston Scientific Scimed, Inc. Bioabsorbable Marker Having Radiopaque Constituents And Method of Using the Same
US20100030149A1 (en) * 2006-10-23 2010-02-04 C.R. Bard, Inc. Breast marker
US20100049302A1 (en) * 2007-03-14 2010-02-25 Sung-Gwon Kang Stent for expending intra luminal
WO2010030370A1 (en) * 2008-09-12 2010-03-18 William A. Cook Australia Pty. Ltd. Radiopaque reinforcing member
US20100262182A1 (en) * 2007-05-15 2010-10-14 Occlutech Gmbh Occlusion Instruments Comprising Bioresorbable Radiopaque Polymeric Materials, As Well As Related Products, Methods And Uses
US20110022161A1 (en) * 2006-06-06 2011-01-27 Rutgers, The State University Of New Jersey Iodinated polymers
US20110034991A1 (en) * 2006-08-07 2011-02-10 Biotronik Vi Patent Ag Endoprosthesis and method for producing same
US20110166439A1 (en) * 2008-05-23 2011-07-07 Marvis Technologies Gmbh Medical instrument
WO2012019090A1 (en) * 2010-08-05 2012-02-09 William A. Cook Australia Pty. Ltd. Stent graft having a marker and a reinforcing and marker ring
US8157862B2 (en) 1997-10-10 2012-04-17 Senorx, Inc. Tissue marking implant
US8177792B2 (en) 2002-06-17 2012-05-15 Senorx, Inc. Plugged tip delivery tube for marker placement
US8219182B2 (en) 1999-02-02 2012-07-10 Senorx, Inc. Cavity-filling biopsy site markers
US8224424B2 (en) 1999-02-02 2012-07-17 Senorx, Inc. Tissue site markers for in vivo imaging
US8311610B2 (en) 2008-01-31 2012-11-13 C. R. Bard, Inc. Biopsy tissue marker
US8361082B2 (en) 1999-02-02 2013-01-29 Senorx, Inc. Marker delivery device with releasable plug
US8401622B2 (en) 2006-12-18 2013-03-19 C. R. Bard, Inc. Biopsy marker with in situ-generated imaging properties
US8447386B2 (en) 2003-05-23 2013-05-21 Senorx, Inc. Marker or filler forming fluid
US8486028B2 (en) 2005-10-07 2013-07-16 Bard Peripheral Vascular, Inc. Tissue marking apparatus having drug-eluting tissue marker
US8498693B2 (en) 1999-02-02 2013-07-30 Senorx, Inc. Intracorporeal marker and marker delivery device
US8579931B2 (en) 1999-06-17 2013-11-12 Bard Peripheral Vascular, Inc. Apparatus for the percutaneous marking of a lesion
US8626269B2 (en) 2003-05-23 2014-01-07 Senorx, Inc. Fibrous marker and intracorporeal delivery thereof
US8634899B2 (en) 2003-11-17 2014-01-21 Bard Peripheral Vascular, Inc. Multi mode imaging marker
US8668737B2 (en) 1997-10-10 2014-03-11 Senorx, Inc. Tissue marking implant
US8670818B2 (en) 2008-12-30 2014-03-11 C. R. Bard, Inc. Marker delivery device for tissue marker placement
US20140094844A1 (en) * 2012-10-01 2014-04-03 Microvention, Inc Catheter Markers
US8718745B2 (en) 2000-11-20 2014-05-06 Senorx, Inc. Tissue site markers for in vivo imaging
USD715442S1 (en) 2013-09-24 2014-10-14 C. R. Bard, Inc. Tissue marker for intracorporeal site identification
USD715942S1 (en) 2013-09-24 2014-10-21 C. R. Bard, Inc. Tissue marker for intracorporeal site identification
USD716450S1 (en) 2013-09-24 2014-10-28 C. R. Bard, Inc. Tissue marker for intracorporeal site identification
USD716451S1 (en) 2013-09-24 2014-10-28 C. R. Bard, Inc. Tissue marker for intracorporeal site identification
US9149341B2 (en) 1999-02-02 2015-10-06 Senorx, Inc Deployment of polysaccharide markers for treating a site within a patient
US9327061B2 (en) 2008-09-23 2016-05-03 Senorx, Inc. Porous bioabsorbable implant
US20170035945A1 (en) * 2006-07-20 2017-02-09 Orbusneich Medical, Inc. Bioabsorbable polymeric composition for a medical device
US9579077B2 (en) 2006-12-12 2017-02-28 C.R. Bard, Inc. Multiple imaging mode tissue marker
US9681876B2 (en) 2013-07-31 2017-06-20 EMBA Medical Limited Methods and devices for endovascular embolization
US9820824B2 (en) 1999-02-02 2017-11-21 Senorx, Inc. Deployment of polysaccharide markers for treating a site within a patent
US9848956B2 (en) 2002-11-18 2017-12-26 Bard Peripheral Vascular, Inc. Self-contained, self-piercing, side-expelling marking apparatus
US10010328B2 (en) 2013-07-31 2018-07-03 NeuVT Limited Endovascular occlusion device with hemodynamically enhanced sealing and anchoring
US10342635B2 (en) 2005-04-20 2019-07-09 Bard Peripheral Vascular, Inc. Marking device with retractable cannula
US10806826B2 (en) 2013-01-09 2020-10-20 Bacterin International, Inc. Bone graft substitute containing a temporary contrast agent and a method of generating such and a method of use thereof
EP4115854A1 (en) * 2015-01-12 2023-01-11 Microvention, Inc. Stent

Families Citing this family (532)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH10508504A (en) * 1994-09-16 1998-08-25 バイオプシス メディカル インコーポレイテッド Method and apparatus for identifying and marking tissue
JP4042998B2 (en) 1997-01-29 2008-02-06 クック インコーポレイテッド Bell bottom modular stent graft
US8172897B2 (en) * 1997-04-15 2012-05-08 Advanced Cardiovascular Systems, Inc. Polymer and metal composite implantable medical devices
US6240616B1 (en) * 1997-04-15 2001-06-05 Advanced Cardiovascular Systems, Inc. Method of manufacturing a medicated porous metal prosthesis
US10028851B2 (en) * 1997-04-15 2018-07-24 Advanced Cardiovascular Systems, Inc. Coatings for controlling erosion of a substrate of an implantable medical device
US6776792B1 (en) * 1997-04-24 2004-08-17 Advanced Cardiovascular Systems Inc. Coated endovascular stent
US5741327A (en) * 1997-05-06 1998-04-21 Global Therapeutics, Inc. Surgical stent featuring radiopaque markers
US6226548B1 (en) 1997-09-24 2001-05-01 Surgical Navigation Technologies, Inc. Percutaneous registration apparatus and method for use in computer-assisted surgical navigation
US6270464B1 (en) * 1998-06-22 2001-08-07 Artemis Medical, Inc. Biopsy localization method and device
US6626939B1 (en) * 1997-12-18 2003-09-30 Boston Scientific Scimed, Inc. Stent-graft with bioabsorbable structural support
US6161034A (en) * 1999-02-02 2000-12-12 Senorx, Inc. Methods and chemical preparations for time-limited marking of biopsy sites
US7713297B2 (en) * 1998-04-11 2010-05-11 Boston Scientific Scimed, Inc. Drug-releasing stent with ceramic-containing layer
US20020058882A1 (en) * 1998-06-22 2002-05-16 Artemis Medical, Incorporated Biopsy localization method and device
US7004962B2 (en) * 1998-07-27 2006-02-28 Schneider (Usa), Inc. Neuroaneurysm occlusion and delivery device and method of using same
EP1051206B1 (en) * 1998-12-01 2008-08-20 Cook Biotech, Inc. A multi-formed collagenous biomaterial medical device
US8177762B2 (en) 1998-12-07 2012-05-15 C. R. Bard, Inc. Septum including at least one identifiable feature, access ports including same, and related methods
US9669113B1 (en) * 1998-12-24 2017-06-06 Devicor Medical Products, Inc. Device and method for safe location and marking of a biopsy cavity
US6356782B1 (en) 1998-12-24 2002-03-12 Vivant Medical, Inc. Subcutaneous cavity marking device and method
US6371904B1 (en) * 1998-12-24 2002-04-16 Vivant Medical, Inc. Subcutaneous cavity marking device and method
US7018401B1 (en) 1999-02-01 2006-03-28 Board Of Regents, The University Of Texas System Woven intravascular devices and methods for making the same and apparatus for delivery of the same
US6173715B1 (en) * 1999-03-01 2001-01-16 Lucent Medical Systems, Inc. Magnetic anatomical marker and method of use
US6790228B2 (en) * 1999-12-23 2004-09-14 Advanced Cardiovascular Systems, Inc. Coating for implantable devices and a method of forming the same
WO2001047438A1 (en) * 1999-12-23 2001-07-05 Edwards Lifesciences Corporation Enhanced visualization of medical implants
US6355058B1 (en) * 1999-12-30 2002-03-12 Advanced Cardiovascular Systems, Inc. Stent with radiopaque coating consisting of particles in a binder
US6575888B2 (en) 2000-01-25 2003-06-10 Biosurface Engineering Technologies, Inc. Bioabsorbable brachytherapy device
DE10004832A1 (en) * 2000-01-31 2001-08-16 Ethicon Gmbh Flat implant with X-ray visible elements
JP3450810B2 (en) * 2000-01-31 2003-09-29 キヤノン株式会社 Aliphatic polyester, method for producing aliphatic polyester and method for recycling cellulose
US6350244B1 (en) * 2000-02-21 2002-02-26 Biopsy Sciences, Llc Bioabsorable markers for use in biopsy procedures
US9522217B2 (en) * 2000-03-15 2016-12-20 Orbusneich Medical, Inc. Medical device with coating for capturing genetically-altered cells and methods for using same
US8460367B2 (en) 2000-03-15 2013-06-11 Orbusneich Medical, Inc. Progenitor endothelial cell capturing with a drug eluting implantable medical device
US8088060B2 (en) * 2000-03-15 2012-01-03 Orbusneich Medical, Inc. Progenitor endothelial cell capturing with a drug eluting implantable medical device
US20050271701A1 (en) * 2000-03-15 2005-12-08 Orbus Medical Technologies, Inc. Progenitor endothelial cell capturing with a drug eluting implantable medical device
JP5030358B2 (en) 2000-03-23 2012-09-19 クック メディカル テクノロジーズ エルエルシー Introducing sheath
US6527801B1 (en) * 2000-04-13 2003-03-04 Advanced Cardiovascular Systems, Inc. Biodegradable drug delivery material for stent
US8109994B2 (en) * 2003-01-10 2012-02-07 Abbott Cardiovascular Systems, Inc. Biodegradable drug delivery material for stent
US7875283B2 (en) * 2000-04-13 2011-01-25 Advanced Cardiovascular Systems, Inc. Biodegradable polymers for use with implantable medical devices
US20030114918A1 (en) * 2000-04-28 2003-06-19 Garrison Michi E. Stent graft assembly and method
WO2001095834A1 (en) * 2000-06-13 2001-12-20 Scimed Life Systems, Inc. Disintegrating stent and method of making same
US6394965B1 (en) * 2000-08-15 2002-05-28 Carbon Medical Technologies, Inc. Tissue marking using biocompatible microparticles
US6589273B1 (en) * 2000-10-02 2003-07-08 Impra, Inc. Apparatus and method for relining a blood vessel
US6783793B1 (en) * 2000-10-26 2004-08-31 Advanced Cardiovascular Systems, Inc. Selective coating of medical devices
EP1545705A4 (en) 2000-11-16 2010-04-28 Microspherix Llc Flexible and/or elastic brachytherapy seed or strand
DE10064596A1 (en) 2000-12-18 2002-06-20 Biotronik Mess & Therapieg Application of a marker element to an implant, especially a stent, comprises introducing a solidifiable material into a recess and solidifying the material in the recess
US6574497B1 (en) * 2000-12-22 2003-06-03 Advanced Cardiovascular Systems, Inc. MRI medical device markers utilizing fluorine-19
US6635082B1 (en) * 2000-12-29 2003-10-21 Advanced Cardiovascular Systems Inc. Radiopaque stent
WO2002070167A1 (en) * 2001-03-05 2002-09-12 Idev Technologies, Inc. Methods for securing strands of woven medical devices
US20020138136A1 (en) * 2001-03-23 2002-09-26 Scimed Life Systems, Inc. Medical device having radio-opacification and barrier layers
DE10123934A1 (en) * 2001-05-17 2002-12-05 Ethicon Gmbh Flat implant
SE519069C2 (en) * 2001-05-21 2003-01-07 Cid Cardivascular Innovation D Surgical marker and an implant
US6585754B2 (en) * 2001-05-29 2003-07-01 Scimed Life Systems, Inc. Absorbable implantable vaso-occlusive member
US6723052B2 (en) * 2001-06-07 2004-04-20 Stanley L. Mills Echogenic medical device
US7201940B1 (en) * 2001-06-12 2007-04-10 Advanced Cardiovascular Systems, Inc. Method and apparatus for thermal spray processing of medical devices
US7727221B2 (en) 2001-06-27 2010-06-01 Cardiac Pacemakers Inc. Method and device for electrochemical formation of therapeutic species in vivo
US6565659B1 (en) * 2001-06-28 2003-05-20 Advanced Cardiovascular Systems, Inc. Stent mounting assembly and a method of using the same to coat a stent
US6786919B1 (en) * 2001-07-10 2004-09-07 Endovascular Technologies, Inc. Self-expanding intravascular device with protector members
US6605047B2 (en) * 2001-09-10 2003-08-12 Vivant Medical, Inc. Biopsy marker delivery system
GB0123596D0 (en) * 2001-10-02 2001-11-21 Smiths Group Plc Medico-surgical devices
US7285304B1 (en) * 2003-06-25 2007-10-23 Advanced Cardiovascular Systems, Inc. Fluid treatment of a polymeric coating on an implantable medical device
US7989018B2 (en) * 2001-09-17 2011-08-02 Advanced Cardiovascular Systems, Inc. Fluid treatment of a polymeric coating on an implantable medical device
US6863683B2 (en) * 2001-09-19 2005-03-08 Abbott Laboratoris Vascular Entities Limited Cold-molding process for loading a stent onto a stent delivery system
US7572287B2 (en) * 2001-10-25 2009-08-11 Boston Scientific Scimed, Inc. Balloon expandable polymer stent with reduced elastic recoil
US6939376B2 (en) * 2001-11-05 2005-09-06 Sun Biomedical, Ltd. Drug-delivery endovascular stent and method for treating restenosis
AU2002360695A1 (en) * 2001-12-19 2003-07-09 Nmt Medical, Inc. Septal occluder and associated methods
US7318833B2 (en) 2001-12-19 2008-01-15 Nmt Medical, Inc. PFO closure device with flexible thrombogenic joint and improved dislodgement resistance
US7147661B2 (en) * 2001-12-20 2006-12-12 Boston Scientific Santa Rosa Corp. Radially expandable stent
JP2005525843A (en) * 2002-01-14 2005-09-02 エヌエムティー メディカル インコーポレイテッド Patent foramen ovale (PFO) occlusion method and apparatus
WO2003082076A2 (en) * 2002-03-25 2003-10-09 Nmt Medical, Inc. Patent foramen ovale (pfo) closure clips
US7140769B2 (en) * 2002-04-12 2006-11-28 Kay George W Radiation sensitive recording plate with orientation identifying marker, method of making, and of using same
US7563025B2 (en) * 2002-04-12 2009-07-21 Kay George W Methods and apparatus for preserving orientation information in radiography images
DE60328677D1 (en) * 2002-05-20 2009-09-17 Kawasumi Lab Inc STENT AND STENT PROSTHESIS
EP1538994A4 (en) 2002-06-05 2008-05-07 Nmt Medical Inc Patent foramen ovale (pfo) closure device with radial and circumferential support
ATE318555T1 (en) * 2002-08-13 2006-03-15 Abbott Lab Vascular Entpr Ltd STENT
US20040034407A1 (en) 2002-08-16 2004-02-19 John Sherry Covered stents with degradable barbs
US20040044399A1 (en) * 2002-09-04 2004-03-04 Ventura Joseph A. Radiopaque links for self-expanding stents
JP2005538780A (en) * 2002-09-13 2005-12-22 リンバテック・コーポレイション Stretched and expanded stents
US7766820B2 (en) 2002-10-25 2010-08-03 Nmt Medical, Inc. Expandable sheath tubing
US20060271168A1 (en) * 2002-10-30 2006-11-30 Klaus Kleine Degradable medical device
WO2004043508A1 (en) * 2002-11-06 2004-05-27 Nmt Medical, Inc. Medical devices utilizing modified shape memory alloy
AU2003290675A1 (en) * 2002-11-07 2004-06-03 Abbott Laboratories Method of loading beneficial agent to a prosthesis by fluid-jet application
US7285287B2 (en) * 2002-11-14 2007-10-23 Synecor, Llc Carbon dioxide-assisted methods of providing biocompatible intraluminal prostheses
US20040098106A1 (en) * 2002-11-14 2004-05-20 Williams Michael S. Intraluminal prostheses and carbon dioxide-assisted methods of impregnating same with pharmacological agents
US20040111146A1 (en) * 2002-12-04 2004-06-10 Mccullagh Orla Stent-graft attachment
US9017373B2 (en) * 2002-12-09 2015-04-28 W.L. Gore & Associates, Inc. Septal closure devices
US8435550B2 (en) * 2002-12-16 2013-05-07 Abbot Cardiovascular Systems Inc. Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device
US7758881B2 (en) * 2004-06-30 2010-07-20 Advanced Cardiovascular Systems, Inc. Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device
US8088158B2 (en) * 2002-12-20 2012-01-03 Boston Scientific Scimed, Inc. Radiopaque ePTFE medical devices
US20040143317A1 (en) * 2003-01-17 2004-07-22 Stinson Jonathan S. Medical devices
US20040260386A1 (en) * 2003-01-31 2004-12-23 Shalaby Shalaby W. Absorbable / biodegradable tubular stent and methods of making the same
US6932930B2 (en) * 2003-03-10 2005-08-23 Synecor, Llc Intraluminal prostheses having polymeric material with selectively modified crystallinity and methods of making same
US7792568B2 (en) * 2003-03-17 2010-09-07 Boston Scientific Scimed, Inc. MRI-visible medical devices
US20040193208A1 (en) * 2003-03-27 2004-09-30 Scimed Life Systems, Inc. Radiopaque embolic protection filter membrane
US7186789B2 (en) * 2003-06-11 2007-03-06 Advanced Cardiovascular Systems, Inc. Bioabsorbable, biobeneficial polyester polymers for use in drug eluting stent coatings
CN1470294A (en) * 2003-07-07 2004-01-28 �й���ѧԺ����Ӧ�û�ѧ�о��� Biodegradable common bile duct built-in carriage and its making method
US8480706B2 (en) 2003-07-14 2013-07-09 W.L. Gore & Associates, Inc. Tubular patent foramen ovale (PFO) closure device with catch system
CA2532112C (en) * 2003-07-14 2012-09-18 Nmt Medical, Inc. Tubular patent foramen ovale (pfo) closure device with catch system
US9861346B2 (en) * 2003-07-14 2018-01-09 W. L. Gore & Associates, Inc. Patent foramen ovale (PFO) closure device with linearly elongating petals
US20050033157A1 (en) * 2003-07-25 2005-02-10 Klein Dean A. Multi-modality marking material and method
US7790141B2 (en) * 2003-08-11 2010-09-07 Pathak Holdings, Llc Radio-opaque compounds, compositions containing same and methods of their synthesis and use
DE602004017750D1 (en) * 2003-08-19 2008-12-24 Nmt Medical Inc Expandable lock hose
US20050064223A1 (en) * 2003-09-22 2005-03-24 Bavaro Vincent Peter Polymeric marker with high radiopacity
US20050065434A1 (en) * 2003-09-22 2005-03-24 Bavaro Vincent P. Polymeric marker with high radiopacity for use in medical devices
US7198675B2 (en) * 2003-09-30 2007-04-03 Advanced Cardiovascular Systems Stent mandrel fixture and method for selectively coating surfaces of a stent
US8014849B2 (en) * 2003-11-21 2011-09-06 Stryker Corporation Rotational markers
US20050113904A1 (en) * 2003-11-25 2005-05-26 Shank Peter J. Composite stent with inner and outer stent elements and method of using the same
US8435285B2 (en) 2003-11-25 2013-05-07 Boston Scientific Scimed, Inc. Composite stent with inner and outer stent elements and method of using the same
US20050273119A1 (en) * 2003-12-09 2005-12-08 Nmt Medical, Inc. Double spiral patent foramen ovale closure clamp
DE10361942A1 (en) * 2003-12-24 2005-07-21 Restate Patent Ag Radioopaque marker for medical implants
US8137397B2 (en) * 2004-02-26 2012-03-20 Boston Scientific Scimed, Inc. Medical devices
US20060142838A1 (en) * 2004-12-29 2006-06-29 Masoud Molaei Medical devices including metallic films and methods for loading and deploying same
US20050197687A1 (en) * 2004-03-02 2005-09-08 Masoud Molaei Medical devices including metallic films and methods for making same
US8998973B2 (en) 2004-03-02 2015-04-07 Boston Scientific Scimed, Inc. Medical devices including metallic films
US8591568B2 (en) * 2004-03-02 2013-11-26 Boston Scientific Scimed, Inc. Medical devices including metallic films and methods for making same
US8992592B2 (en) * 2004-12-29 2015-03-31 Boston Scientific Scimed, Inc. Medical devices including metallic films
US8632580B2 (en) * 2004-12-29 2014-01-21 Boston Scientific Scimed, Inc. Flexible medical devices including metallic films
US7901447B2 (en) 2004-12-29 2011-03-08 Boston Scientific Scimed, Inc. Medical devices including a metallic film and at least one filament
JP2007526087A (en) 2004-03-03 2007-09-13 エヌエムティー メディカル, インコーポレイティッド Delivery / recovery system for septal occluder
TWI434676B (en) 2004-03-19 2014-04-21 Merck Sharp & Dohme X-ray visible drug delivery device
JP2007530120A (en) * 2004-03-26 2007-11-01 ヌヴァシヴ インコーポレイテッド Porous implant for spinal disc nucleus pulposus replacement
US20050234336A1 (en) * 2004-03-26 2005-10-20 Beckman Andrew T Apparatus and method for marking tissue
US20050214339A1 (en) * 2004-03-29 2005-09-29 Yiwen Tang Biologically degradable compositions for medical applications
US20050267524A1 (en) * 2004-04-09 2005-12-01 Nmt Medical, Inc. Split ends closure device
US8361110B2 (en) * 2004-04-26 2013-01-29 W.L. Gore & Associates, Inc. Heart-shaped PFO closure device
US20050288481A1 (en) * 2004-04-30 2005-12-29 Desnoyer Jessica R Design of poly(ester amides) for the control of agent-release from polymeric compositions
US7842053B2 (en) 2004-05-06 2010-11-30 Nmt Medical, Inc. Double coil occluder
US8308760B2 (en) * 2004-05-06 2012-11-13 W.L. Gore & Associates, Inc. Delivery systems and methods for PFO closure device with two anchors
CA2563298A1 (en) 2004-05-07 2005-11-24 Nmt Medical, Inc. Catching mechanisms for tubular septal occluder
WO2005112833A1 (en) * 2004-05-20 2005-12-01 Pearsalls Limited Improvements in and relating to surgical implants
US7758892B1 (en) * 2004-05-20 2010-07-20 Boston Scientific Scimed, Inc. Medical devices having multiple layers
AU2010236494B2 (en) 2004-05-25 2013-05-30 Covidien Lp Vascular stenting for aneurysms
US8118864B1 (en) * 2004-05-25 2012-02-21 Endovascular Technologies, Inc. Drug delivery endovascular graft
US8617234B2 (en) * 2004-05-25 2013-12-31 Covidien Lp Flexible vascular occluding device
EP1750619B1 (en) 2004-05-25 2013-07-24 Covidien LP Flexible vascular occluding device
US20060206200A1 (en) 2004-05-25 2006-09-14 Chestnut Medical Technologies, Inc. Flexible vascular occluding device
US8628564B2 (en) 2004-05-25 2014-01-14 Covidien Lp Methods and apparatus for luminal stenting
US20050283226A1 (en) * 2004-06-18 2005-12-22 Scimed Life Systems, Inc. Medical devices
US8568469B1 (en) 2004-06-28 2013-10-29 Advanced Cardiovascular Systems, Inc. Stent locking element and a method of securing a stent on a delivery system
US8241554B1 (en) 2004-06-29 2012-08-14 Advanced Cardiovascular Systems, Inc. Method of forming a stent pattern on a tube
US7140532B2 (en) * 2004-07-25 2006-11-28 Aricoga Creative Development, Llc Container with integral compartments
US8747878B2 (en) 2006-04-28 2014-06-10 Advanced Cardiovascular Systems, Inc. Method of fabricating an implantable medical device by controlling crystalline structure
US7731890B2 (en) * 2006-06-15 2010-06-08 Advanced Cardiovascular Systems, Inc. Methods of fabricating stents with enhanced fracture toughness
US8778256B1 (en) 2004-09-30 2014-07-15 Advanced Cardiovascular Systems, Inc. Deformation of a polymer tube in the fabrication of a medical article
US20060020330A1 (en) * 2004-07-26 2006-01-26 Bin Huang Method of fabricating an implantable medical device with biaxially oriented polymers
US7971333B2 (en) * 2006-05-30 2011-07-05 Advanced Cardiovascular Systems, Inc. Manufacturing process for polymetric stents
US8747879B2 (en) * 2006-04-28 2014-06-10 Advanced Cardiovascular Systems, Inc. Method of fabricating an implantable medical device to reduce chance of late inflammatory response
US20060041102A1 (en) * 2004-08-23 2006-02-23 Advanced Cardiovascular Systems, Inc. Implantable devices comprising biologically absorbable polymers having constant rate of degradation and methods for fabricating the same
US9283099B2 (en) * 2004-08-25 2016-03-15 Advanced Cardiovascular Systems, Inc. Stent-catheter assembly with a releasable connection for stent retention
EP1791496B1 (en) 2004-08-31 2019-07-31 C.R. Bard, Inc. Self-sealing ptfe graft with kink resistance
US7229471B2 (en) * 2004-09-10 2007-06-12 Advanced Cardiovascular Systems, Inc. Compositions containing fast-leaching plasticizers for improved performance of medical devices
US7695506B2 (en) * 2004-09-21 2010-04-13 Boston Scientific Scimed, Inc. Atraumatic connections for multi-component stents
CA2581677C (en) * 2004-09-24 2014-07-29 Nmt Medical, Inc. Occluder device double securement system for delivery/recovery of such occluder device
US8173062B1 (en) 2004-09-30 2012-05-08 Advanced Cardiovascular Systems, Inc. Controlled deformation of a polymer tube in fabricating a medical article
US8043553B1 (en) 2004-09-30 2011-10-25 Advanced Cardiovascular Systems, Inc. Controlled deformation of a polymer tube with a restraining surface in fabricating a medical article
US7875233B2 (en) 2004-09-30 2011-01-25 Advanced Cardiovascular Systems, Inc. Method of fabricating a biaxially oriented implantable medical device
US20060094957A1 (en) * 2004-11-01 2006-05-04 Mueller Richard L Jr Marker and cut down guide assembly for human mammary duct procedures and method
ES2478283T3 (en) 2004-11-10 2014-07-21 Boston Scientific Scimed, Inc. Atraumatic vascular endoprosthesis with reduced deployment force
US7455688B2 (en) * 2004-11-12 2008-11-25 Con Interventional Systems, Inc. Ostial stent
US20060127443A1 (en) * 2004-12-09 2006-06-15 Helmus Michael N Medical devices having vapor deposited nanoporous coatings for controlled therapeutic agent delivery
KR100511618B1 (en) * 2005-01-17 2005-08-31 이경범 Multi-layer coating of drug release controllable coronary stent and method for manufacturing the same
US8083805B2 (en) * 2005-08-16 2011-12-27 Poly-Med, Inc. Absorbable endo-urological devices and applications therefor
US8083806B2 (en) * 2005-02-04 2011-12-27 Poly-Med, Inc. Radiation and radiochemically sterilized fiber-reinforced, composite urinogenital stents
JP2008529597A (en) * 2005-02-04 2008-08-07 ポリ−メッド インコーポレイティド Fiber reinforced composite absorbable intraurethral stent
US20060201601A1 (en) * 2005-03-03 2006-09-14 Icon Interventional Systems, Inc. Flexible markers
US7947022B2 (en) 2005-03-04 2011-05-24 C. R. Bard, Inc. Access port identification systems and methods
US7785302B2 (en) 2005-03-04 2010-08-31 C. R. Bard, Inc. Access port identification systems and methods
US9474888B2 (en) 2005-03-04 2016-10-25 C. R. Bard, Inc. Implantable access port including a sandwiched radiopaque insert
US8202259B2 (en) 2005-03-04 2012-06-19 C. R. Bard, Inc. Systems and methods for identifying an access port
EP1698907A1 (en) * 2005-03-04 2006-09-06 Cardiatis Société Anonyme Interventional medical device for use in MRI
US8029482B2 (en) 2005-03-04 2011-10-04 C. R. Bard, Inc. Systems and methods for radiographically identifying an access port
WO2006102213A1 (en) 2005-03-18 2006-09-28 Nmt Medical, Inc. Catch member for pfo occluder
US20060216431A1 (en) * 2005-03-28 2006-09-28 Kerrigan Cameron K Electrostatic abluminal coating of a stent crimped on a balloon catheter
US20060224226A1 (en) * 2005-03-31 2006-10-05 Bin Huang In-vivo radial orientation of a polymeric implantable medical device
US7381048B2 (en) * 2005-04-12 2008-06-03 Advanced Cardiovascular Systems, Inc. Stents with profiles for gripping a balloon catheter and molds for fabricating stents
US10307581B2 (en) 2005-04-27 2019-06-04 C. R. Bard, Inc. Reinforced septum for an implantable medical device
US8147455B2 (en) 2005-04-27 2012-04-03 C. R. Bard, Inc. Infusion apparatuses and methods of use
DE602006019587D1 (en) 2005-04-27 2011-02-24 Bard Inc C R Syringe pumping system for injection of contrast agent in an intravenous line
US9265634B2 (en) * 2005-05-13 2016-02-23 Boston Scientific Scimed, Inc. Integrated stent repositioning and retrieval loop
US7854760B2 (en) * 2005-05-16 2010-12-21 Boston Scientific Scimed, Inc. Medical devices including metallic films
US7291166B2 (en) * 2005-05-18 2007-11-06 Advanced Cardiovascular Systems, Inc. Polymeric stent patterns
EP1883371B1 (en) 2005-05-25 2015-10-07 Covidien LP System and method for delivering and deploying and occluding device within a vessel
US20060276910A1 (en) * 2005-06-01 2006-12-07 Jan Weber Endoprostheses
WO2006133130A2 (en) * 2005-06-03 2006-12-14 Nuvasive, Inc. Fibrous spinal implant and method of implantation
GB0514891D0 (en) * 2005-07-20 2005-08-24 Pearsalls Ltd Improvements in and relating to implants
WO2007001472A2 (en) 2005-06-17 2007-01-04 C. R. Bard, Inc. Vascular graft with kink resistance after clamping
US7622070B2 (en) * 2005-06-20 2009-11-24 Advanced Cardiovascular Systems, Inc. Method of manufacturing an implantable polymeric medical device
DE102005030472A1 (en) 2005-06-28 2007-01-04 Joachim-Georg Pfeffer Rod-shaped body
US20070038176A1 (en) * 2005-07-05 2007-02-15 Jan Weber Medical devices with machined layers for controlled communications with underlying regions
US7658880B2 (en) * 2005-07-29 2010-02-09 Advanced Cardiovascular Systems, Inc. Polymeric stent polishing method and apparatus
US7297758B2 (en) * 2005-08-02 2007-11-20 Advanced Cardiovascular Systems, Inc. Method for extending shelf-life of constructs of semi-crystallizable polymers
US20070038290A1 (en) * 2005-08-15 2007-02-15 Bin Huang Fiber reinforced composite stents
US7476245B2 (en) * 2005-08-16 2009-01-13 Advanced Cardiovascular Systems, Inc. Polymeric stent patterns
CN103637840A (en) 2005-08-23 2014-03-19 史密夫和内修有限公司 Telemetric orthopaedic implant
US9248034B2 (en) * 2005-08-23 2016-02-02 Advanced Cardiovascular Systems, Inc. Controlled disintegrating implantable medical devices
US20070045255A1 (en) * 2005-08-23 2007-03-01 Klaus Kleine Laser induced plasma machining with an optimized process gas
US20070045252A1 (en) * 2005-08-23 2007-03-01 Klaus Kleine Laser induced plasma machining with a process gas
GB0707671D0 (en) * 2007-04-20 2007-05-30 Invibio Ltd Fiducial marker
JP2009512521A (en) * 2005-10-24 2009-03-26 エヌエムティー メディカル, インコーポレイティッド Radiopaque bioabsorbable occluder
JP5280852B2 (en) 2005-11-09 2013-09-04 シー・アール・バード・インコーポレーテッド Grafts and stent grafts with radiopaque markers
US7867547B2 (en) 2005-12-19 2011-01-11 Advanced Cardiovascular Systems, Inc. Selectively coating luminal surfaces of stents
EP1962695A1 (en) * 2005-12-22 2008-09-03 NMT Medical, Inc. Catch members for occluder devices
US20070151961A1 (en) * 2006-01-03 2007-07-05 Klaus Kleine Fabrication of an implantable medical device with a modified laser beam
US20070156230A1 (en) * 2006-01-04 2007-07-05 Dugan Stephen R Stents with radiopaque markers
US8840660B2 (en) * 2006-01-05 2014-09-23 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US20070158880A1 (en) * 2006-01-06 2007-07-12 Vipul Bhupendra Dave Methods of making bioabsorbable drug delivery devices comprised of solvent cast tubes
US7951185B1 (en) 2006-01-06 2011-05-31 Advanced Cardiovascular Systems, Inc. Delivery of a stent at an elevated temperature
US20070162110A1 (en) * 2006-01-06 2007-07-12 Vipul Bhupendra Dave Bioabsorbable drug delivery devices
US20070160672A1 (en) * 2006-01-06 2007-07-12 Vipul Bhupendra Dave Methods of making bioabsorbable drug delivery devices comprised of solvent cast films
US20070179219A1 (en) * 2006-01-31 2007-08-02 Bin Huang Method of fabricating an implantable medical device using gel extrusion and charge induced orientation
US8089029B2 (en) * 2006-02-01 2012-01-03 Boston Scientific Scimed, Inc. Bioabsorbable metal medical device and method of manufacture
US8152833B2 (en) 2006-02-22 2012-04-10 Tyco Healthcare Group Lp Embolic protection systems having radiopaque filter mesh
US20070203564A1 (en) * 2006-02-28 2007-08-30 Boston Scientific Scimed, Inc. Biodegradable implants having accelerated biodegradation properties in vivo
US9849216B2 (en) * 2006-03-03 2017-12-26 Smith & Nephew, Inc. Systems and methods for delivering a medicament
US20070224244A1 (en) * 2006-03-22 2007-09-27 Jan Weber Corrosion resistant coatings for biodegradable metallic implants
US20070238979A1 (en) * 2006-03-23 2007-10-11 Medtronic Vascular, Inc. Reference Devices for Placement in Heart Structures for Visualization During Heart Valve Procedures
US20070224235A1 (en) * 2006-03-24 2007-09-27 Barron Tenney Medical devices having nanoporous coatings for controlled therapeutic agent delivery
US8187620B2 (en) * 2006-03-27 2012-05-29 Boston Scientific Scimed, Inc. Medical devices comprising a porous metal oxide or metal material and a polymer coating for delivering therapeutic agents
US8551135B2 (en) * 2006-03-31 2013-10-08 W.L. Gore & Associates, Inc. Screw catch mechanism for PFO occluder and method of use
US8870913B2 (en) 2006-03-31 2014-10-28 W.L. Gore & Associates, Inc. Catch system with locking cap for patent foramen ovale (PFO) occluder
EP2004068B1 (en) * 2006-03-31 2018-08-15 W.L. Gore & Associates, Inc. Deformable flap catch mechanism for occluder device
US7964210B2 (en) * 2006-03-31 2011-06-21 Abbott Cardiovascular Systems Inc. Degradable polymeric implantable medical devices with a continuous phase and discrete phase
WO2007126931A2 (en) * 2006-03-31 2007-11-08 Ev3 Inc. Embolic protection devices having radiopaque markers
US8048150B2 (en) * 2006-04-12 2011-11-01 Boston Scientific Scimed, Inc. Endoprosthesis having a fiber meshwork disposed thereon
US9155646B2 (en) * 2006-04-27 2015-10-13 Brs Holdings, Llc Composite stent with bioremovable ceramic flakes
US9101505B2 (en) * 2006-04-27 2015-08-11 Brs Holdings, Llc Composite stent
US20070254012A1 (en) * 2006-04-28 2007-11-01 Ludwig Florian N Controlled degradation and drug release in stents
US8003156B2 (en) * 2006-05-04 2011-08-23 Advanced Cardiovascular Systems, Inc. Rotatable support elements for stents
US20070264303A1 (en) * 2006-05-12 2007-11-15 Liliana Atanasoska Coating for medical devices comprising an inorganic or ceramic oxide and a therapeutic agent
EP2023869B1 (en) * 2006-05-12 2019-09-18 Cardinal Health Switzerland 515 GmbH Balloon expandable bioabsorbable drug eluting flexible stent
US8535368B2 (en) 2006-05-19 2013-09-17 Boston Scientific Scimed, Inc. Apparatus for loading and delivering a stent
US7761968B2 (en) * 2006-05-25 2010-07-27 Advanced Cardiovascular Systems, Inc. Method of crimping a polymeric stent
US7951194B2 (en) * 2006-05-26 2011-05-31 Abbott Cardiovascular Sysetms Inc. Bioabsorbable stent with radiopaque coating
US8752267B2 (en) 2006-05-26 2014-06-17 Abbott Cardiovascular Systems Inc. Method of making stents with radiopaque markers
US8343530B2 (en) * 2006-05-30 2013-01-01 Abbott Cardiovascular Systems Inc. Polymer-and polymer blend-bioceramic composite implantable medical devices
US7842737B2 (en) 2006-09-29 2010-11-30 Abbott Cardiovascular Systems Inc. Polymer blend-bioceramic composite implantable medical devices
US20070282434A1 (en) * 2006-05-30 2007-12-06 Yunbing Wang Copolymer-bioceramic composite implantable medical devices
US7959940B2 (en) * 2006-05-30 2011-06-14 Advanced Cardiovascular Systems, Inc. Polymer-bioceramic composite implantable medical devices
US20080058916A1 (en) * 2006-05-31 2008-03-06 Bin Huang Method of fabricating polymeric self-expandable stent
US8486135B2 (en) 2006-06-01 2013-07-16 Abbott Cardiovascular Systems Inc. Implantable medical devices fabricated from branched polymers
US20070282433A1 (en) * 2006-06-01 2007-12-06 Limon Timothy A Stent with retention protrusions formed during crimping
US8034287B2 (en) 2006-06-01 2011-10-11 Abbott Cardiovascular Systems Inc. Radiation sterilization of medical devices
US20070281073A1 (en) * 2006-06-01 2007-12-06 Gale David C Enhanced adhesion of drug delivery coatings on stents
US20080124372A1 (en) * 2006-06-06 2008-05-29 Hossainy Syed F A Morphology profiles for control of agent release rates from polymer matrices
US20070288084A1 (en) * 2006-06-09 2007-12-13 Medlogics Device Corporation Implantable Stent with Degradable Portions
US20070286941A1 (en) * 2006-06-13 2007-12-13 Bin Huang Surface treatment of a polymeric stent
US8603530B2 (en) 2006-06-14 2013-12-10 Abbott Cardiovascular Systems Inc. Nanoshell therapy
US8048448B2 (en) * 2006-06-15 2011-11-01 Abbott Cardiovascular Systems Inc. Nanoshells for drug delivery
US8535372B1 (en) 2006-06-16 2013-09-17 Abbott Cardiovascular Systems Inc. Bioabsorbable stent with prohealing layer
US8333000B2 (en) 2006-06-19 2012-12-18 Advanced Cardiovascular Systems, Inc. Methods for improving stent retention on a balloon catheter
US20070290412A1 (en) * 2006-06-19 2007-12-20 John Capek Fabricating a stent with selected properties in the radial and axial directions
US8017237B2 (en) 2006-06-23 2011-09-13 Abbott Cardiovascular Systems, Inc. Nanoshells on polymers
US9072820B2 (en) * 2006-06-26 2015-07-07 Advanced Cardiovascular Systems, Inc. Polymer composite stent with polymer particles
US20070299511A1 (en) * 2006-06-27 2007-12-27 Gale David C Thin stent coating
US8128688B2 (en) * 2006-06-27 2012-03-06 Abbott Cardiovascular Systems Inc. Carbon coating on an implantable device
US8815275B2 (en) 2006-06-28 2014-08-26 Boston Scientific Scimed, Inc. Coatings for medical devices comprising a therapeutic agent and a metallic material
US7794776B1 (en) 2006-06-29 2010-09-14 Abbott Cardiovascular Systems Inc. Modification of polymer stents with radiation
WO2008002778A2 (en) * 2006-06-29 2008-01-03 Boston Scientific Limited Medical devices with selective coating
US7740791B2 (en) * 2006-06-30 2010-06-22 Advanced Cardiovascular Systems, Inc. Method of fabricating a stent with features by blow molding
US20080009938A1 (en) * 2006-07-07 2008-01-10 Bin Huang Stent with a radiopaque marker and method for making the same
US20080008654A1 (en) * 2006-07-07 2008-01-10 Boston Scientific Scimed, Inc. Medical devices having a temporary radiopaque coating
US7823263B2 (en) 2006-07-11 2010-11-02 Abbott Cardiovascular Systems Inc. Method of removing stent islands from a stent
US20080014244A1 (en) * 2006-07-13 2008-01-17 Gale David C Implantable medical devices and coatings therefor comprising physically crosslinked block copolymers
US7757543B2 (en) 2006-07-13 2010-07-20 Advanced Cardiovascular Systems, Inc. Radio frequency identification monitoring of stents
US7998404B2 (en) * 2006-07-13 2011-08-16 Advanced Cardiovascular Systems, Inc. Reduced temperature sterilization of stents
US7794495B2 (en) * 2006-07-17 2010-09-14 Advanced Cardiovascular Systems, Inc. Controlled degradation of stents
US7886419B2 (en) * 2006-07-18 2011-02-15 Advanced Cardiovascular Systems, Inc. Stent crimping apparatus and method
US20090216063A1 (en) * 2008-01-29 2009-08-27 Biocompatibles Uk Limited Bio-absorbable brachytherapy strands
US9265866B2 (en) * 2006-08-01 2016-02-23 Abbott Cardiovascular Systems Inc. Composite polymeric and metallic stent with radiopacity
US8016879B2 (en) * 2006-08-01 2011-09-13 Abbott Cardiovascular Systems Inc. Drug delivery after biodegradation of the stent scaffolding
US20080091262A1 (en) * 2006-10-17 2008-04-17 Gale David C Drug delivery after biodegradation of the stent scaffolding
US8052743B2 (en) 2006-08-02 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis with three-dimensional disintegration control
US20080294039A1 (en) * 2006-08-04 2008-11-27 Senorx, Inc. Assembly with hemostatic and radiographically detectable pellets
DE102006038233A1 (en) * 2006-08-07 2008-02-14 Biotronik Vi Patent Ag Marker composite for medical implants
US9173733B1 (en) 2006-08-21 2015-11-03 Abbott Cardiovascular Systems Inc. Tracheobronchial implantable medical device and methods of use
US20080085293A1 (en) * 2006-08-22 2008-04-10 Jenchen Yang Drug eluting stent and therapeutic methods using c-Jun N-terminal kinase inhibitor
US20080065200A1 (en) * 2006-09-07 2008-03-13 Trireme Medical, Inc. Bifurcated prostheses having differential drug coatings
US7923022B2 (en) * 2006-09-13 2011-04-12 Advanced Cardiovascular Systems, Inc. Degradable polymeric implantable medical devices with continuous phase and discrete phase
JP2010503469A (en) 2006-09-14 2010-02-04 ボストン サイエンティフィック リミテッド Medical device having drug-eluting film
JP2010503489A (en) * 2006-09-15 2010-02-04 ボストン サイエンティフィック リミテッド Biodegradable endoprosthesis and method for producing the same
US8128689B2 (en) 2006-09-15 2012-03-06 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis with biostable inorganic layers
CA2663271A1 (en) * 2006-09-15 2008-03-20 Boston Scientific Limited Bioerodible endoprostheses and methods of making the same
CA2663220A1 (en) * 2006-09-15 2008-03-20 Boston Scientific Limited Medical devices and methods of making the same
WO2008036548A2 (en) * 2006-09-18 2008-03-27 Boston Scientific Limited Endoprostheses
EP2073764A2 (en) * 2006-09-18 2009-07-01 Boston Scientific Limited Controlling biodegradation of a medical instrument
US20080077180A1 (en) * 2006-09-26 2008-03-27 Nmt Medical, Inc. Scaffold for tubular septal occluder device and techniques for attachment
WO2008042311A1 (en) * 2006-09-28 2008-04-10 Nmt Medical. Inc. Perforated expandable implant recovery sheath
WO2008045184A1 (en) * 2006-10-05 2008-04-17 Boston Scientific Limited Polymer-free coatings for medical devices formed by plasma electrolytic deposition
US9198749B2 (en) 2006-10-12 2015-12-01 C. R. Bard, Inc. Vascular grafts with multiple channels and methods for making
BRPI0717392A2 (en) 2006-10-22 2013-10-15 Idev Technologies Inc METHODS FOR FIXING WIRE END AND RESULTING DEVICES
US10413284B2 (en) 2006-11-07 2019-09-17 Corvia Medical, Inc. Atrial pressure regulation with control, sensing, monitoring and therapy delivery
US10610210B2 (en) 2006-11-07 2020-04-07 Corvia Medical, Inc. Methods for deploying a prosthesis
US8460372B2 (en) 2006-11-07 2013-06-11 Dc Devices, Inc. Prosthesis for reducing intra-cardiac pressure having an embolic filter
US20110257723A1 (en) 2006-11-07 2011-10-20 Dc Devices, Inc. Devices and methods for coronary sinus pressure relief
EP2097012A4 (en) 2006-11-07 2012-08-15 David Stephen Celermajer Devices and methods for the treatment of heart failure
US9232997B2 (en) 2006-11-07 2016-01-12 Corvia Medical, Inc. Devices and methods for retrievable intra-atrial implants
US9642986B2 (en) 2006-11-08 2017-05-09 C. R. Bard, Inc. Resource information key for an insertable medical device
US9265912B2 (en) 2006-11-08 2016-02-23 C. R. Bard, Inc. Indicia informative of characteristics of insertable medical devices
US7981150B2 (en) 2006-11-09 2011-07-19 Boston Scientific Scimed, Inc. Endoprosthesis with coatings
FR2908630A1 (en) * 2006-11-16 2008-05-23 Creaspine Surgical implant e.g. prosthetic implant, blank manufacturing method, involves co-extruding radio-visible material with radio-transparent material so as to obtain insert of radio-visible material at inside radio-transparent material
US8114159B2 (en) 2006-11-20 2012-02-14 Depuy Spine, Inc. Anterior spinal vessel protector
US8099849B2 (en) 2006-12-13 2012-01-24 Abbott Cardiovascular Systems Inc. Optimizing fracture toughness of polymeric stent
EP2125065B1 (en) 2006-12-28 2010-11-17 Boston Scientific Limited Bioerodible endoprostheses and methods of making same
US7942104B2 (en) * 2007-01-22 2011-05-17 Nuvasive, Inc. 3-dimensional embroidery structures via tension shaping
US7946236B2 (en) * 2007-01-31 2011-05-24 Nuvasive, Inc. Using zigzags to create three-dimensional embroidered structures
US20100320639A1 (en) * 2007-02-08 2010-12-23 Christopher Reah Medical Implants with Pre-Settled Cores and Related Methods
BRPI0807260A2 (en) * 2007-02-09 2014-06-10 Taheri Laduca Llc "IMPLANTABLE STENT AND METHOD OF MANUFACTURING A TUBULAR GRAFT"
EP1959391A1 (en) * 2007-02-13 2008-08-20 BrainLAB AG Determination of the three dimensional contour path of an anatomical structure
EP1958585A1 (en) * 2007-02-13 2008-08-20 BrainLAB AG Mutatable marker device
EP2121055B1 (en) * 2007-02-13 2014-04-02 Abbott Cardiovascular Systems Inc. Mri compatible, radiopaque alloys for use in medical devices
US8431149B2 (en) 2007-03-01 2013-04-30 Boston Scientific Scimed, Inc. Coated medical devices for abluminal drug delivery
US8070797B2 (en) 2007-03-01 2011-12-06 Boston Scientific Scimed, Inc. Medical device with a porous surface for delivery of a therapeutic agent
DE102007012964A1 (en) * 2007-03-06 2008-09-11 Phenox Gmbh Implant for influencing blood flow
US20080234572A1 (en) * 2007-03-23 2008-09-25 Civco Medical Instruments Co., Inc. Fiducial marker with absorbable connecting sleeve and absorbable spacer for imaging localization
US20080243228A1 (en) * 2007-03-28 2008-10-02 Yunbing Wang Implantable medical devices fabricated from block copolymers
US8545548B2 (en) * 2007-03-30 2013-10-01 DePuy Synthes Products, LLC Radiopaque markers for implantable stents and methods for manufacturing the same
US8067054B2 (en) 2007-04-05 2011-11-29 Boston Scientific Scimed, Inc. Stents with ceramic drug reservoir layer and methods of making and using the same
US9005242B2 (en) 2007-04-05 2015-04-14 W.L. Gore & Associates, Inc. Septal closure device with centering mechanism
US8262723B2 (en) 2007-04-09 2012-09-11 Abbott Cardiovascular Systems Inc. Implantable medical devices fabricated from polymer blends with star-block copolymers
US8409270B2 (en) * 2007-04-16 2013-04-02 Boston Scientific Scimed, Inc. Radiopaque compositions, stents and methods of preparation
US20100286778A1 (en) * 2007-04-18 2010-11-11 Lukas Eisermann Textile-Based Spinal Implant and Related Methods
US9138562B2 (en) 2007-04-18 2015-09-22 W.L. Gore & Associates, Inc. Flexible catheter system
US7976915B2 (en) * 2007-05-23 2011-07-12 Boston Scientific Scimed, Inc. Endoprosthesis with select ceramic morphology
US7829008B2 (en) * 2007-05-30 2010-11-09 Abbott Cardiovascular Systems Inc. Fabricating a stent from a blow molded tube
US7959857B2 (en) * 2007-06-01 2011-06-14 Abbott Cardiovascular Systems Inc. Radiation sterilization of medical devices
US8202528B2 (en) * 2007-06-05 2012-06-19 Abbott Cardiovascular Systems Inc. Implantable medical devices with elastomeric block copolymer coatings
US8293260B2 (en) * 2007-06-05 2012-10-23 Abbott Cardiovascular Systems Inc. Elastomeric copolymer coatings containing poly (tetramethyl carbonate) for implantable medical devices
US20080306582A1 (en) * 2007-06-05 2008-12-11 Yunbing Wang Implantable medical devices with elastomeric copolymer coatings
US8425591B1 (en) 2007-06-11 2013-04-23 Abbott Cardiovascular Systems Inc. Methods of forming polymer-bioceramic composite medical devices with bioceramic particles
ES2651269T3 (en) 2007-06-20 2018-01-25 Medical Components, Inc. Venous reservoir with molded indications and / or radiopacas
US8048441B2 (en) 2007-06-25 2011-11-01 Abbott Cardiovascular Systems, Inc. Nanobead releasing medical devices
US20090005853A1 (en) * 2007-06-26 2009-01-01 Karim Osman Integration Of Markers Into Bar Arms
US7901452B2 (en) * 2007-06-27 2011-03-08 Abbott Cardiovascular Systems Inc. Method to fabricate a stent having selected morphology to reduce restenosis
US7955381B1 (en) 2007-06-29 2011-06-07 Advanced Cardiovascular Systems, Inc. Polymer-bioceramic composite implantable medical device with different types of bioceramic particles
DE102007030751B4 (en) * 2007-07-02 2009-06-10 Acandis Gmbh & Co. Kg Method of making a stent
US8002823B2 (en) * 2007-07-11 2011-08-23 Boston Scientific Scimed, Inc. Endoprosthesis coating
US7942926B2 (en) * 2007-07-11 2011-05-17 Boston Scientific Scimed, Inc. Endoprosthesis coating
EP2180915B1 (en) 2007-07-19 2017-10-04 Medical Components, Inc. Venous access port assembly with x-ray discernable indicia
EP2187988B1 (en) * 2007-07-19 2013-08-21 Boston Scientific Limited Endoprosthesis having a non-fouling surface
US9610432B2 (en) * 2007-07-19 2017-04-04 Innovative Medical Devices, Llc Venous access port assembly with X-ray discernable indicia
US7931683B2 (en) 2007-07-27 2011-04-26 Boston Scientific Scimed, Inc. Articles having ceramic coated surfaces
US8815273B2 (en) * 2007-07-27 2014-08-26 Boston Scientific Scimed, Inc. Drug eluting medical devices having porous layers
US8221822B2 (en) * 2007-07-31 2012-07-17 Boston Scientific Scimed, Inc. Medical device coating by laser cladding
JP2010535541A (en) * 2007-08-03 2010-11-25 ボストン サイエンティフィック リミテッド Coating for medical devices with large surface area
US8282681B2 (en) * 2007-08-13 2012-10-09 Nuvasive, Inc. Bioresorbable spinal implant and related methods
US8052745B2 (en) * 2007-09-13 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis
US9034007B2 (en) * 2007-09-21 2015-05-19 Insera Therapeutics, Inc. Distal embolic protection devices with a variable thickness microguidewire and methods for their use
US9393137B2 (en) * 2007-09-24 2016-07-19 Boston Scientific Scimed, Inc. Method for loading a stent into a delivery system
US8246998B2 (en) * 2007-11-01 2012-08-21 Boston Scientific Scimed, Inc. Injectable biodegradable particles
US20090118813A1 (en) * 2007-11-02 2009-05-07 Torsten Scheuermann Nano-patterned implant surfaces
US7938855B2 (en) 2007-11-02 2011-05-10 Boston Scientific Scimed, Inc. Deformable underlayer for stent
US8216632B2 (en) 2007-11-02 2012-07-10 Boston Scientific Scimed, Inc. Endoprosthesis coating
US8029554B2 (en) * 2007-11-02 2011-10-04 Boston Scientific Scimed, Inc. Stent with embedded material
US20090118809A1 (en) * 2007-11-02 2009-05-07 Torsten Scheuermann Endoprosthesis with porous reservoir and non-polymer diffusion layer
US9579496B2 (en) 2007-11-07 2017-02-28 C. R. Bard, Inc. Radiopaque and septum-based indicators for a multi-lumen implantable port
US20090143855A1 (en) * 2007-11-29 2009-06-04 Boston Scientific Scimed, Inc. Medical Device Including Drug-Loaded Fibers
US8118857B2 (en) * 2007-11-29 2012-02-21 Boston Scientific Corporation Medical articles that stimulate endothelial cell migration
US9101698B2 (en) * 2007-12-05 2015-08-11 Abbott Cardiovascular Systems Inc. Bioabsorbable stent with radiopaque layer and method of fabrication
US20100008970A1 (en) * 2007-12-14 2010-01-14 Boston Scientific Scimed, Inc. Drug-Eluting Endoprosthesis
US7972373B2 (en) * 2007-12-19 2011-07-05 Advanced Technologies And Regenerative Medicine, Llc Balloon expandable bioabsorbable stent with a single stress concentration region interconnecting adjacent struts
US9592100B2 (en) * 2007-12-31 2017-03-14 St. Jude Medical, Atrial Fibrillation Division, Inc. Method and apparatus for encoding catheters with markers for identifying with imaging systems
US8986318B2 (en) 2008-06-03 2015-03-24 Jeffrey Scott Smith Pedicle depth measuring apparatus
US8740956B2 (en) 2008-01-10 2014-06-03 J. Scott Smith Pedicle screw
US9668775B2 (en) * 2008-06-03 2017-06-06 Jeffrey Scott Smith Pedicle screw
US8715332B2 (en) * 2008-01-15 2014-05-06 Boston Scientific Scimed, Inc. Expandable stent delivery system with outer sheath
JP5526038B2 (en) 2008-01-17 2014-06-18 ボストン サイエンティフィック サイムド,インコーポレイテッド Stent with anti-migration feature
US20090204203A1 (en) * 2008-02-07 2009-08-13 Medtronic Vascular, Inc. Bioabsorbable Stent Having a Radiopaque Marker
US20130165967A1 (en) 2008-03-07 2013-06-27 W.L. Gore & Associates, Inc. Heart occlusion devices
US8377135B1 (en) 2008-03-31 2013-02-19 Nuvasive, Inc. Textile-based surgical implant and related methods
EP2271380B1 (en) 2008-04-22 2013-03-20 Boston Scientific Scimed, Inc. Medical devices having a coating of inorganic material
US8932346B2 (en) 2008-04-24 2015-01-13 Boston Scientific Scimed, Inc. Medical devices having inorganic particle layers
US7998192B2 (en) * 2008-05-09 2011-08-16 Boston Scientific Scimed, Inc. Endoprostheses
US20090287145A1 (en) * 2008-05-15 2009-11-19 Altura Interventional, Inc. Devices and methods for treatment of abdominal aortic aneurysms
US20090287301A1 (en) * 2008-05-16 2009-11-19 Boston Scientific, Scimed Inc. Coating for medical implants
US8236046B2 (en) 2008-06-10 2012-08-07 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
US8449603B2 (en) 2008-06-18 2013-05-28 Boston Scientific Scimed, Inc. Endoprosthesis coating
US20100004733A1 (en) * 2008-07-02 2010-01-07 Boston Scientific Scimed, Inc. Implants Including Fractal Structures
US7985252B2 (en) * 2008-07-30 2011-07-26 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
US9119906B2 (en) 2008-09-24 2015-09-01 Integran Technologies, Inc. In-vivo biodegradable medical implant
US8382824B2 (en) * 2008-10-03 2013-02-26 Boston Scientific Scimed, Inc. Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides
EP2364115B1 (en) 2008-10-15 2019-02-20 Smith & Nephew, Inc. Composite internal fixators
WO2010048052A1 (en) 2008-10-22 2010-04-29 Boston Scientific Scimed, Inc. Shape memory tubular stent with grooves
DE102008043642A1 (en) 2008-11-11 2010-05-12 Biotronik Vi Patent Ag endoprosthesis
US8932271B2 (en) 2008-11-13 2015-01-13 C. R. Bard, Inc. Implantable medical devices including septum-based indicators
US11890443B2 (en) 2008-11-13 2024-02-06 C. R. Bard, Inc. Implantable medical devices including septum-based indicators
US8231980B2 (en) * 2008-12-03 2012-07-31 Boston Scientific Scimed, Inc. Medical implants including iridium oxide
DE102008054845A1 (en) 2008-12-18 2010-07-01 Biotronik Vi Patent Ag Device and method for producing the same
US20100160862A1 (en) * 2008-12-22 2010-06-24 Cook Incorporated Variable stiffness introducer sheath with transition zone
US20100291182A1 (en) * 2009-01-21 2010-11-18 Arsenal Medical, Inc. Drug-Loaded Fibers
US8151682B2 (en) 2009-01-26 2012-04-10 Boston Scientific Scimed, Inc. Atraumatic stent and method and apparatus for making the same
GB0901779D0 (en) * 2009-02-05 2009-03-11 Mandeco 569 Ltd An artificial ligament and method of manufacture
CA2753079C (en) 2009-02-27 2018-04-10 Halifax Biomedical Inc. Device and method for bone imaging
US8267992B2 (en) * 2009-03-02 2012-09-18 Boston Scientific Scimed, Inc. Self-buffering medical implants
US8071156B2 (en) * 2009-03-04 2011-12-06 Boston Scientific Scimed, Inc. Endoprostheses
US20100274352A1 (en) * 2009-04-24 2010-10-28 Boston Scientific Scrimed, Inc. Endoprosthesis with Selective Drug Coatings
US8287937B2 (en) * 2009-04-24 2012-10-16 Boston Scientific Scimed, Inc. Endoprosthese
US9936892B1 (en) * 2009-05-04 2018-04-10 Cortex Manufacturing Inc. Systems and methods for providing a fiducial marker
US8858613B2 (en) * 2010-09-20 2014-10-14 Altura Medical, Inc. Stent graft delivery systems and associated methods
US9265633B2 (en) 2009-05-20 2016-02-23 480 Biomedical, Inc. Drug-eluting medical implants
US8992601B2 (en) * 2009-05-20 2015-03-31 480 Biomedical, Inc. Medical implants
JP5820370B2 (en) * 2009-05-20 2015-11-24 アーセナル メディカル, インコーポレイテッド Medical implant
US9014787B2 (en) 2009-06-01 2015-04-21 Focal Therapeutics, Inc. Bioabsorbable target for diagnostic or therapeutic procedure
EP2442860B1 (en) 2009-06-15 2019-03-27 Perflow Medical Ltd. Apparatus for allowing blood flow through an occluded vessel
US9636094B2 (en) 2009-06-22 2017-05-02 W. L. Gore & Associates, Inc. Sealing device and delivery system
US20120029556A1 (en) 2009-06-22 2012-02-02 Masters Steven J Sealing device and delivery system
WO2011002641A1 (en) 2009-06-30 2011-01-06 Boston Scientific Scimed, Inc. Endoprosthesis and endoprosthesis delivery system and method
WO2011005847A1 (en) 2009-07-07 2011-01-13 C. R. Bard, Inc. Extensible internal bolster for a medical device
US8529596B2 (en) 2009-07-08 2013-09-10 Concentric Medical, Inc. Vascular and bodily duct treatment devices and methods
US9889238B2 (en) * 2009-07-21 2018-02-13 Abbott Cardiovascular Systems Inc. Biodegradable stent with adjustable degradation rate
US8889823B2 (en) * 2009-07-21 2014-11-18 Abbott Cardiovascular Systems Inc. Method to make poly(L-lactide) stent with tunable degradation rate
US20110022158A1 (en) * 2009-07-22 2011-01-27 Boston Scientific Scimed, Inc. Bioerodible Medical Implants
US9173817B2 (en) 2009-08-24 2015-11-03 Arsenal Medical, Inc. In situ forming hemostatic foam implants
US20110202016A1 (en) * 2009-08-24 2011-08-18 Arsenal Medical, Inc. Systems and methods relating to polymer foams
US10420862B2 (en) 2009-08-24 2019-09-24 Aresenal AAA, LLC. In-situ forming foams for treatment of aneurysms
US9044580B2 (en) 2009-08-24 2015-06-02 Arsenal Medical, Inc. In-situ forming foams with outer layer
US20110054589A1 (en) * 2009-08-27 2011-03-03 Boston Scientific Scimed, Inc. Stent with variable cross section braiding filament and method for making same
US8753708B2 (en) * 2009-09-02 2014-06-17 Cardiac Pacemakers, Inc. Solventless method for forming a coating on a medical electrical lead body
US9757107B2 (en) 2009-09-04 2017-09-12 Corvia Medical, Inc. Methods and devices for intra-atrial shunts having adjustable sizes
EP2475329B1 (en) 2009-09-10 2015-12-02 Boston Scientific Scimed, Inc. Endoprosthesis with filament repositioning or retrieval member and guard structure
US20110071613A1 (en) 2009-09-21 2011-03-24 Boston Scientific Scimed, Inc. Integrated stent retrieval loop adapted for snare removal and/or optimized purse stringing
US10052220B2 (en) 2009-10-09 2018-08-21 Boston Scientific Scimed, Inc. Stomach bypass for the treatment of obesity
EP2501294B1 (en) 2009-11-17 2018-08-15 C.R. Bard, Inc. Overmolded access port including anchoring and identification features
US20110190774A1 (en) * 2009-11-18 2011-08-04 Julian Nikolchev Methods and apparatus for performing an arthroscopic procedure using surgical navigation
WO2011068915A1 (en) * 2009-12-01 2011-06-09 Altura Medical, Inc. Modular endograft devices and associated systems and methods
US20110190870A1 (en) * 2009-12-30 2011-08-04 Boston Scientific Scimed, Inc. Covered Stent for Vascular Closure
CA2785041A1 (en) 2010-01-29 2011-08-04 Dc Devices, Inc. Devices and methods for reducing venous pressure
US8808353B2 (en) 2010-01-30 2014-08-19 Abbott Cardiovascular Systems Inc. Crush recoverable polymer scaffolds having a low crossing profile
US8568471B2 (en) 2010-01-30 2013-10-29 Abbott Cardiovascular Systems Inc. Crush recoverable polymer scaffolds
WO2011119573A1 (en) * 2010-03-23 2011-09-29 Boston Scientific Scimed, Inc. Surface treated bioerodible metal endoprostheses
US8808357B2 (en) * 2010-04-06 2014-08-19 Poly-Med, Inc. Radiopaque iodinated and iodide-containing crystalline absorbable aliphatic polymeric materials and applications thereof
US8389041B2 (en) 2010-06-17 2013-03-05 Abbott Cardiovascular Systems, Inc. Systems and methods for rotating and coating an implantable device
WO2012019145A1 (en) 2010-08-06 2012-02-09 Endoshape, Inc. Radiopaque shape memory polymers for medical devices
DE102010044746A1 (en) * 2010-09-08 2012-03-08 Phenox Gmbh Implant for influencing the blood flow in arteriovenous malformations
EP2462961A3 (en) * 2010-12-08 2014-08-27 Biotronik AG Implant made of biocorrodible material and with a coating containing a tissue adhesive
US9717420B2 (en) * 2010-12-20 2017-08-01 Empire Technology Development Llc Implantable apparatus for facilitating imaging-based diagnoses
USD676955S1 (en) 2010-12-30 2013-02-26 C. R. Bard, Inc. Implantable access port
USD682416S1 (en) 2010-12-30 2013-05-14 C. R. Bard, Inc. Implantable access port
US9194058B2 (en) 2011-01-31 2015-11-24 Arsenal Medical, Inc. Electrospinning process for manufacture of multi-layered structures
US8968626B2 (en) 2011-01-31 2015-03-03 Arsenal Medical, Inc. Electrospinning process for manufacture of multi-layered structures
US9034240B2 (en) 2011-01-31 2015-05-19 Arsenal Medical, Inc. Electrospinning process for fiber manufacture
KR101680420B1 (en) * 2011-02-04 2016-11-28 콘센트릭 메디칼, 인크. Vascular and bodily duct treatment devices and methods
EP3156004B1 (en) * 2011-02-04 2018-04-11 Concentric Medical, Inc. Vascular and bodily duct treatment devices
AU2012214279A1 (en) 2011-02-10 2013-08-22 Corvia Medical, Inc. Apparatus and methods to create and maintain an intra-atrial pressure relief opening
ES2400120B1 (en) * 2011-06-15 2014-02-25 Mba Incorporado, S.L. DEVICE FOR INSERTION OF TANTAL MARKERS IN SURGICAL INSERTS.
US8726483B2 (en) 2011-07-29 2014-05-20 Abbott Cardiovascular Systems Inc. Methods for uniform crimping and deployment of a polymer scaffold
US20130035665A1 (en) * 2011-08-05 2013-02-07 W. L. Gore & Associates, Inc. Polymer-Based Occlusion Devices, Systems and Methods
US9770232B2 (en) 2011-08-12 2017-09-26 W. L. Gore & Associates, Inc. Heart occlusion devices
EP2747800A1 (en) 2011-08-26 2014-07-02 Ella-CS, s.r.o. Self-expandable biodegradable stent made of clad radiopaque fibers covered with biodegradable elastic foil and therapeutic agent and method of preparation thereof
US8993831B2 (en) 2011-11-01 2015-03-31 Arsenal Medical, Inc. Foam and delivery system for treatment of postpartum hemorrhage
CN102440856A (en) * 2011-12-09 2012-05-09 微创医疗器械(上海)有限公司 Biodegradable stent capable of being seen under X rays and preparation method of biodegradable stent
WO2013096965A1 (en) 2011-12-22 2013-06-27 Dc Devices, Inc. Methods and devices for intra-atrial devices having selectable flow rates
GB2499377B (en) * 2012-02-01 2014-04-30 Cook Medical Technologies Llc Implantable medical device
US9005155B2 (en) 2012-02-03 2015-04-14 Dc Devices, Inc. Devices and methods for treating heart failure
US10588611B2 (en) 2012-04-19 2020-03-17 Corvia Medical Inc. Implant retention attachment and method of use
US20130289389A1 (en) 2012-04-26 2013-10-31 Focal Therapeutics Surgical implant for marking soft tissue
US9233015B2 (en) 2012-06-15 2016-01-12 Trivascular, Inc. Endovascular delivery system with an improved radiopaque marker scheme
US9649480B2 (en) 2012-07-06 2017-05-16 Corvia Medical, Inc. Devices and methods of treating or ameliorating diastolic heart failure through pulmonary valve intervention
CN105050549B (en) 2012-08-10 2017-07-21 阿尔图拉医疗公司 Stent delivery system and associated method
CA2887879A1 (en) 2012-10-25 2014-05-01 Beatrice Vial Radiopaque marker for bioresorbable stents
US9114001B2 (en) 2012-10-30 2015-08-25 Covidien Lp Systems for attaining a predetermined porosity of a vascular device
US9452070B2 (en) 2012-10-31 2016-09-27 Covidien Lp Methods and systems for increasing a density of a region of a vascular device
US9943427B2 (en) 2012-11-06 2018-04-17 Covidien Lp Shaped occluding devices and methods of using the same
US10828019B2 (en) 2013-01-18 2020-11-10 W.L. Gore & Associates, Inc. Sealing device and delivery system
DE102013100984B4 (en) * 2013-01-31 2019-03-21 Acandis Gmbh Grid mesh for a medical implant or instrument, implant and instrument with such a mesh and set with such an implant or instrument
DE102013201707A1 (en) * 2013-02-01 2014-08-07 Aesculap Ag Vascular prosthesis e.g. aorta sine prosthesis, for use as vessel patch i.e. two-dimensional sheet, of patient for e.g. replacement of defective wall, has orientation unit extending along direction of prosthesis and comprising interruptions
DE102013201698A1 (en) * 2013-02-01 2014-08-07 Aesculap Ag Vascular prosthesis e.g. bypass prosthesis has radiopaque threads that are extended in longitudinal direction, and are comprised of metal or metal alloy threads
US9157174B2 (en) 2013-02-05 2015-10-13 Covidien Lp Vascular device for aneurysm treatment and providing blood flow into a perforator vessel
CN105073143A (en) 2013-02-08 2015-11-18 恩多沙普公司 Radiopaque polymers for medical devices
US9775636B2 (en) 2013-03-12 2017-10-03 Corvia Medical, Inc. Devices, systems, and methods for treating heart failure
US10561509B2 (en) 2013-03-13 2020-02-18 DePuy Synthes Products, Inc. Braided stent with expansion ring and method of delivery
WO2014152252A1 (en) 2013-03-14 2014-09-25 Active Implants Corporation Meniscus prosthetic devices with anti-migration or radiopaque features
US20160175085A1 (en) * 2013-03-14 2016-06-23 Volcano Corporation Enhanced fluorogenic endoluminal filter structure
US8679150B1 (en) 2013-03-15 2014-03-25 Insera Therapeutics, Inc. Shape-set textile structure based mechanical thrombectomy methods
EP3620203A1 (en) 2013-03-15 2020-03-11 Insera Therapeutics, Inc. Vascular treatment devices
US8690907B1 (en) 2013-03-15 2014-04-08 Insera Therapeutics, Inc. Vascular treatment methods
WO2014200594A1 (en) 2013-03-15 2014-12-18 Endoshape, Inc. Polymer compositions with enhanced radiopacity
WO2014144809A1 (en) 2013-03-15 2014-09-18 Altura Medical, Inc. Endograft device delivery systems and associated methods
US8715314B1 (en) 2013-03-15 2014-05-06 Insera Therapeutics, Inc. Vascular treatment measurement methods
KR101498584B1 (en) * 2013-05-15 2015-03-04 주식회사 스텐다드싸이텍 Stent to prevent migration
CA2919536C (en) * 2013-08-09 2018-01-02 Boston Scientific Scimed, Inc. Atraumatic stents including radiopaque connectors and methods
US9320628B2 (en) * 2013-09-09 2016-04-26 Boston Scientific Scimed, Inc. Endoprosthesis devices including biostable and bioabsorable regions
US10675450B2 (en) 2014-03-12 2020-06-09 Corvia Medical, Inc. Devices and methods for treating heart failure
DE102014005994A1 (en) * 2014-04-23 2015-10-29 Marvis Medical Gmbh Rod-shaped body and medical instrument
US9808230B2 (en) 2014-06-06 2017-11-07 W. L. Gore & Associates, Inc. Sealing device and delivery system
JP6799526B2 (en) 2014-07-23 2020-12-16 コルヴィア メディカル インコーポレイテッド Equipment and methods for the treatment of heart failure
AU2015292332A1 (en) 2014-07-25 2017-02-16 Focal Therapeutics, Inc. Implantable devices and techniques for oncoplastic surgery
US9883898B2 (en) 2014-08-07 2018-02-06 Jeffrey Scott Smith Pedicle screw with electro-conductive coating or portion
EP2990061A1 (en) * 2014-08-26 2016-03-02 Maastricht University Radiopaque composition and preparation thereof
US10206796B2 (en) * 2014-08-27 2019-02-19 DePuy Synthes Products, Inc. Multi-strand implant with enhanced radiopacity
EP3188678A1 (en) 2014-09-01 2017-07-12 Carbofix In Orthopedics LLC Composite material spinal implant
US9931357B2 (en) 2014-10-02 2018-04-03 Cytosorbents Corporation Use of gastrointestinally administered porous enteron sorbent polymers to prevent or treat radiation induced mucositis, esophagitis, enteritis, colitis, and gastrointestinal acute radiation syndrome
DE102014115533B4 (en) * 2014-10-24 2017-11-02 Acandis Gmbh & Co. Kg Medical device for intravascular treatment, thrombectomy device with such a device and manufacturing method
US10016188B2 (en) * 2015-02-10 2018-07-10 Teleflex Innovation S.à.r.l. Closure device for sealing percutaneous opening in a vessel
US9999527B2 (en) 2015-02-11 2018-06-19 Abbott Cardiovascular Systems Inc. Scaffolds having radiopaque markers
US9700443B2 (en) 2015-06-12 2017-07-11 Abbott Cardiovascular Systems Inc. Methods for attaching a radiopaque marker to a scaffold
DE102016116919B4 (en) 2015-11-04 2018-05-17 Biotronik Ag X-ray marker for an endoprosthesis
CN106913383B (en) * 2015-12-25 2020-04-21 先健科技(深圳)有限公司 Developing structure and implantable medical device with same
CN108697423A (en) 2016-02-16 2018-10-23 伊瑟拉医疗公司 The part flow arrangement of suction unit and anchoring
US10022255B2 (en) 2016-04-11 2018-07-17 Idev Technologies, Inc. Stent delivery system having anisotropic sheath
US10568754B2 (en) 2016-05-13 2020-02-25 Boston Scientific Scimed, Inc. Protective apparatus for use in gastrointestinal tract
US10470904B2 (en) 2016-05-18 2019-11-12 Boston Scientific Scimed, Inc. Stent retrieval system
US10076428B2 (en) 2016-08-25 2018-09-18 DePuy Synthes Products, Inc. Expansion ring for a braided stent
US10292851B2 (en) 2016-09-30 2019-05-21 DePuy Synthes Products, Inc. Self-expanding device delivery apparatus with dual function bump
JP7097166B2 (en) * 2016-10-04 2022-07-07 康宏 正林 Flexible stent
WO2018125806A1 (en) 2016-12-29 2018-07-05 Boston Scientific Scimed, Inc. Hydration delivery system for stents
CN106621077A (en) * 2017-02-06 2017-05-10 浙江荣诚医疗科技有限公司 Hollowed-out gold mark and gold mark location device
KR102416460B1 (en) 2017-08-14 2022-07-05 보스톤 싸이엔티픽 싸이메드 인코포레이티드 medical stents
US11413112B2 (en) * 2017-10-13 2022-08-16 Viscus Biologics, Llc Radiopaque tissue marker
KR102436996B1 (en) 2017-10-25 2022-08-26 보스톤 싸이엔티픽 싸이메드 인코포레이티드 Stents with atraumatic spacers
JP2019084309A (en) * 2017-11-10 2019-06-06 教生 毛利 Artificial blood vessel
CN111417361B (en) * 2017-12-01 2023-08-11 C·R·巴德股份有限公司 Adjustable vascular grafts for customized inside diameter reduction and related methods
US10893870B2 (en) * 2018-05-03 2021-01-19 Stryker Corporation Vaso-occlusive device
EP3597155A1 (en) * 2018-07-17 2020-01-22 Cook Medical Technologies LLC Stent having a stent body and detachable anchor portion
AU2019204522A1 (en) 2018-07-30 2020-02-13 DePuy Synthes Products, Inc. Systems and methods of manufacturing and using an expansion ring
US10456280B1 (en) 2018-08-06 2019-10-29 DePuy Synthes Products, Inc. Systems and methods of using a braided implant
US10278848B1 (en) 2018-08-06 2019-05-07 DePuy Synthes Products, Inc. Stent delivery with expansion assisting delivery wire
US20200100889A1 (en) * 2018-10-02 2020-04-02 Cook Medical Technologies Llc Radiopacity modulated radiopaque marker and stent graft using same
US11678970B2 (en) 2018-12-04 2023-06-20 Boston Scientific Scimed, Inc. Device for anastomotic bypass
US11389286B2 (en) 2018-12-05 2022-07-19 Boston Scientific Scimed, Inc. Esophageal atresia bridge device
US11039944B2 (en) 2018-12-27 2021-06-22 DePuy Synthes Products, Inc. Braided stent system with one or more expansion rings
WO2020168181A1 (en) 2019-02-14 2020-08-20 Videra Surgical Inc. Fiducial marker for oncological and other procedures
US11364030B2 (en) 2019-02-15 2022-06-21 Boston Scientific Scimed, Inc. Medical device for treating esophageal atresia
US11504546B2 (en) 2019-02-28 2022-11-22 Cowles Ventures, Llc Needle guidance device for brachytherapy and method of use
CN114025695A (en) 2019-03-12 2022-02-08 碳固定脊柱股份有限公司 Spinal implant of composite material
US11524176B2 (en) 2019-03-14 2022-12-13 Cowles Ventures, Llc Locator for placement of fiducial support device method
US11406489B2 (en) 2019-10-07 2022-08-09 Cornell University Implant with fiducial markers
EP4061291A1 (en) 2019-11-18 2022-09-28 Boston Scientific Scimed Inc. Stent with improved anti-migration properties
US11903767B2 (en) 2019-11-27 2024-02-20 View Point Medical, Inc. Composite tissue markers detectable via multiple detection modalities
US11882992B2 (en) * 2019-11-27 2024-01-30 View Point Medical, Inc. Composite tissue markers detectable via multiple detection modalities including radiopaque element
KR102453419B1 (en) * 2020-01-31 2022-10-11 주식회사 플로스코리아 Biopsy marker
CN115361927A (en) * 2020-04-07 2022-11-18 佐里安医疗公司 Self-expanding biodegradable stent woven from bio-alloy
US20220072272A1 (en) * 2020-09-08 2022-03-10 Covidien Lp Catheter including a bamboo structural support member
WO2022143895A1 (en) * 2020-12-30 2022-07-07 杭州唯强医疗科技有限公司 Intracavitary plugging device
US20220296249A1 (en) * 2021-03-16 2022-09-22 Rhode Island Hospital Endovascular coil device for embolization of blood vessels
CN114767202B (en) * 2022-04-24 2023-03-24 惠州市顺美医疗科技有限公司 Intracranial dense mesh support and preparation method thereof

Citations (17)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3918455A (en) * 1974-04-29 1975-11-11 Albany Int Corp Combined surgical suture and needle
US4471779A (en) * 1976-08-25 1984-09-18 Becton, Dickinson And Company Miniature balloon catheter
US5370691A (en) * 1993-01-26 1994-12-06 Target Therapeutics, Inc. Intravascular inflatable stent
US5376376A (en) * 1992-01-13 1994-12-27 Li; Shu-Tung Resorbable vascular wound dressings
US5441517A (en) * 1991-11-08 1995-08-15 Kensey Nash Corporation Hemostatic puncture closure system and method of use
US5603722A (en) * 1995-06-06 1997-02-18 Quanam Medical Corporation Intravascular stent
US5628787A (en) * 1993-01-19 1997-05-13 Schneider (Usa) Inc. Clad composite stent
US5632771A (en) * 1993-07-23 1997-05-27 Cook Incorporated Flexible stent having a pattern formed from a sheet of material
US5639777A (en) * 1993-11-30 1997-06-17 G.D. Searle & Co. 1,4,5-triphenyl pyrazolyl compounds for the treatment of inflammation and inflammation-related disorders
US5675146A (en) * 1992-09-25 1997-10-07 Texaco Inc. Naturally occurring radioactive material contamination detection means
US5676146A (en) * 1996-09-13 1997-10-14 Osteotech, Inc. Surgical implant containing a resorbable radiopaque marker and method of locating such within a body
US5716397A (en) * 1996-12-06 1998-02-10 Medtronic, Inc. Annuloplasty device with removable stiffening element
US5756127A (en) * 1996-10-29 1998-05-26 Wright Medical Technology, Inc. Implantable bioresorbable string of calcium sulfate beads
US5762625A (en) * 1992-09-08 1998-06-09 Kabushikikaisha Igaki Iryo Sekkei Luminal stent and device for inserting luminal stent
US6174329B1 (en) * 1996-08-22 2001-01-16 Advanced Cardiovascular Systems, Inc. Protective coating for a stent with intermediate radiopaque coating
US6174330B1 (en) * 1997-08-01 2001-01-16 Schneider (Usa) Inc Bioabsorbable marker having radiopaque constituents
US6340367B1 (en) * 1997-08-01 2002-01-22 Boston Scientific Scimed, Inc. Radiopaque markers and methods of using the same

Family Cites Families (106)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3297033A (en) * 1963-10-31 1967-01-10 American Cyanamid Co Surgical sutures
US4202349A (en) 1978-04-24 1980-05-13 Jones James W Radiopaque vessel markers
DE2910749C2 (en) 1979-03-19 1982-11-25 Dr. Eduard Fresenius, Chemisch-pharmazeutische Industrie KG, 6380 Bad Homburg Catheter with contrast stripes
SE424401B (en) 1979-06-06 1982-07-19 Bowald S BLODKERLSPROTES
US4475972A (en) 1981-10-01 1984-10-09 Ontario Research Foundation Implantable material
US4523849A (en) 1982-02-11 1985-06-18 The United States Of America As Represented By The United States Department Of Energy Front lighted optical tooling method and apparatus
SE445884B (en) 1982-04-30 1986-07-28 Medinvent Sa DEVICE FOR IMPLANTATION OF A RODFORM PROTECTION
NL8302561A (en) * 1983-07-04 1985-02-01 Unilever Nv CATALYTIC PREPARATION OF CARBONAMIDES.
EP0183372A1 (en) 1984-10-19 1986-06-04 RAYCHEM CORPORATION (a Delaware corporation) Prosthetic stent
US4787391A (en) * 1985-06-17 1988-11-29 Elefteriades John A Anastomotic marking device and related method
US4738740A (en) 1985-11-21 1988-04-19 Corvita Corporation Method of forming implantable vascular grafts
US4681110A (en) 1985-12-02 1987-07-21 Wiktor Dominik M Catheter arrangement having a blood vessel liner, and method of using it
US4693237A (en) 1986-01-21 1987-09-15 Hoffman Richard B Radiopaque coded ring markers for use in identifying surgical grafts
SE453258B (en) 1986-04-21 1988-01-25 Medinvent Sa ELASTIC, SELF-EXPANDING PROTEST AND PROCEDURE FOR ITS MANUFACTURING
US4722344A (en) 1986-05-23 1988-02-02 Critikon, Inc. Radiopaque polyurethanes and catheters formed therefrom
US5024232A (en) 1986-10-07 1991-06-18 The Research Foundation Of State University Of Ny Novel radiopaque heavy metal polymer complexes, compositions of matter and articles prepared therefrom
FI81498C (en) 1987-01-13 1990-11-12 Biocon Oy SURGICAL MATERIAL OCH INSTRUMENT.
IT1202558B (en) 1987-02-17 1989-02-09 Alberto Arpesani INTERNAL PROSTHESIS FOR THE REPLACEMENT OF A PART OF THE HUMAN BODY PARTICULARLY IN THE VASCULAR OPERATIONS
US5527337A (en) 1987-06-25 1996-06-18 Duke University Bioabsorbable stent and method of making the same
US5059211A (en) 1987-06-25 1991-10-22 Duke University Absorbable vascular stent
US4989608A (en) * 1987-07-02 1991-02-05 Ratner Adam V Device construction and method facilitating magnetic resonance imaging of foreign objects in a body
DE3802158A1 (en) * 1987-08-11 1989-02-23 Hoechst Ag DEVICE FOR APPLICATION OF IMPLANTS
AU4191989A (en) 1988-08-24 1990-03-23 Marvin J. Slepian Biodegradable polymeric endoluminal sealing
US5085629A (en) 1988-10-06 1992-02-04 Medical Engineering Corporation Biodegradable stent
US5178146A (en) * 1988-11-03 1993-01-12 Giese William L Grid and patient alignment system for use with MRI and other imaging modalities
FI85223C (en) 1988-11-10 1992-03-25 Biocon Oy BIODEGRADERANDE SURGICAL IMPLANT OCH MEDEL.
DE9010130U1 (en) 1989-07-13 1990-09-13 American Medical Systems, Inc., Minnetonka, Minn., Us
US5015183A (en) 1989-08-07 1991-05-14 Fenick Thomas J Locating device and method of placing a tooth implant
US5133660A (en) 1989-08-07 1992-07-28 Fenick Thomas J Device for locating the optimum position for a tooth implant
WO1991010766A1 (en) 1990-01-15 1991-07-25 Albany International Corp. Braid structure
JPH05502179A (en) 1990-02-28 1993-04-22 メドトロニック インコーポレーテッド Tubular organ drug elution device
US5545208A (en) 1990-02-28 1996-08-13 Medtronic, Inc. Intralumenal drug eluting prosthesis
US5229431A (en) 1990-06-15 1993-07-20 Corvita Corporation Crack-resistant polycarbonate urethane polymer prostheses and the like
CA2038605C (en) 1990-06-15 2000-06-27 Leonard Pinchuk Crack-resistant polycarbonate urethane polymer prostheses and the like
US5108421A (en) * 1990-10-01 1992-04-28 Quinton Instrument Company Insertion assembly and method of inserting a vessel plug into the body of a patient
US5160341A (en) 1990-11-08 1992-11-03 Advanced Surgical Intervention, Inc. Resorbable urethral stent and apparatus for its insertion
US5163951A (en) 1990-12-27 1992-11-17 Corvita Corporation Mesh composite graft
US5116360A (en) 1990-12-27 1992-05-26 Corvita Corporation Mesh composite graft
US5354257A (en) 1991-01-29 1994-10-11 Med Institute, Inc. Minimally invasive medical device for providing a radiation treatment
CA2060635A1 (en) 1991-02-12 1992-08-13 Keith D'alessio Bioabsorbable medical implants
EP0576517B1 (en) 1991-03-25 1997-05-07 Meadox Medicals Inc. Vascular prosthesis
US5383925A (en) 1992-09-14 1995-01-24 Meadox Medicals, Inc. Three-dimensional braided soft tissue prosthesis
US5256158A (en) 1991-05-17 1993-10-26 Act Medical, Inc. Device having a radiopaque marker for endoscopic accessories and method of making same
US5591172A (en) 1991-06-14 1997-01-07 Ams Medinvent S.A. Transluminal implantation device
US5527354A (en) 1991-06-28 1996-06-18 Cook Incorporated Stent formed of half-round wire
US5320100A (en) * 1991-09-16 1994-06-14 Atrium Medical Corporation Implantable prosthetic device having integral patency diagnostic indicia
US5500013A (en) 1991-10-04 1996-03-19 Scimed Life Systems, Inc. Biodegradable drug delivery vascular stent
US5464450A (en) 1991-10-04 1995-11-07 Scimed Lifesystems Inc. Biodegradable drug delivery vascular stent
WO1993006792A1 (en) 1991-10-04 1993-04-15 Scimed Life Systems, Inc. Biodegradable drug delivery vascular stent
US5366504A (en) 1992-05-20 1994-11-22 Boston Scientific Corporation Tubular medical prosthesis
JP2961287B2 (en) 1991-10-18 1999-10-12 グンゼ株式会社 Biological duct dilator, method for producing the same, and stent
CA2087132A1 (en) * 1992-01-31 1993-08-01 Michael S. Williams Stent capable of attachment within a body lumen
US5203777A (en) 1992-03-19 1993-04-20 Lee Peter Y Radiopaque marker system for a tubular device
US5591224A (en) 1992-03-19 1997-01-07 Medtronic, Inc. Bioelastomeric stent
US5201757A (en) 1992-04-03 1993-04-13 Schneider (Usa) Inc. Medial region deployment of radially self-expanding stents
DE69333161T2 (en) 1992-05-08 2004-06-03 Schneider (Usa) Inc., Plymouth Stent for the esophagus
US5177170A (en) 1992-07-02 1993-01-05 Miles Inc. Radiopaque polyurethanes
US5562725A (en) 1992-09-14 1996-10-08 Meadox Medicals Inc. Radially self-expanding implantable intraluminal device
ATE137656T1 (en) 1992-10-31 1996-05-15 Schneider Europ Ag ARRANGEMENT FOR IMPLANTING SELF-EXPANDING ENDPROSTHESES
BE1006440A3 (en) 1992-12-21 1994-08-30 Dereume Jean Pierre Georges Em Luminal endoprosthesis AND METHOD OF PREPARATION.
US5419760A (en) 1993-01-08 1995-05-30 Pdt Systems, Inc. Medicament dispensing stent for prevention of restenosis of a blood vessel
US5346981A (en) 1993-01-13 1994-09-13 Miles Inc. Radiopaque polyurethanes
US5423849A (en) 1993-01-15 1995-06-13 Target Therapeutics, Inc. Vasoocclusion device containing radiopaque fibers
US5630840A (en) 1993-01-19 1997-05-20 Schneider (Usa) Inc Clad composite stent
US5415546A (en) 1993-03-23 1995-05-16 Cox, Sr.; Ronald W. Radiopaque dental composite and materials
US5405402A (en) 1993-04-14 1995-04-11 Intermedics Orthopedics, Inc. Implantable prosthesis with radiographic marker
US5464650A (en) 1993-04-26 1995-11-07 Medtronic, Inc. Intravascular stent and method
US5320602A (en) 1993-05-14 1994-06-14 Wilson-Cook Medical, Inc. Peel-away endoscopic retrograde cholangio pancreatography catheter and a method for using the same
US5735892A (en) 1993-08-18 1998-04-07 W. L. Gore & Associates, Inc. Intraluminal stent graft
US5498227A (en) 1993-09-15 1996-03-12 Mawad; Michel E. Retrievable, shielded radiotherapy implant
US5429617A (en) 1993-12-13 1995-07-04 The Spectranetics Corporation Radiopaque tip marker for alignment of a catheter within a body
US5445117A (en) * 1994-01-31 1995-08-29 Mendler; Charles Adjustable valve system for a multi-valve internal combustion engine
US5609627A (en) 1994-02-09 1997-03-11 Boston Scientific Technology, Inc. Method for delivering a bifurcated endoluminal prosthesis
US5556413A (en) 1994-03-11 1996-09-17 Advanced Cardiovascular Systems, Inc. Coiled stent with locking ends
EP0679372B1 (en) 1994-04-25 1999-07-28 Advanced Cardiovascular Systems, Inc. Radiopaque stent markers
US5629077A (en) 1994-06-27 1997-05-13 Advanced Cardiovascular Systems, Inc. Biodegradable mesh and film stent
US5433727A (en) 1994-08-16 1995-07-18 Sideris; Eleftherios B. Centering buttoned device for the occlusion of large defects for occluding
ATE186650T1 (en) 1994-08-19 1999-12-15 Biomat Bv RADIATION OPERASIVE POLYMERS AND METHOD FOR THE PRODUCTION THEREOF
IL115755A0 (en) 1994-10-27 1996-01-19 Medinol Ltd X-ray visible stent
US5628755A (en) 1995-02-20 1997-05-13 Schneider (Europe) A.G. Balloon catheter and stent delivery system
US5674277A (en) 1994-12-23 1997-10-07 Willy Rusch Ag Stent for placement in a body tube
US5591226A (en) 1995-01-23 1997-01-07 Schneider (Usa) Inc. Percutaneous stent-graft and method for delivery thereof
US5683449A (en) * 1995-02-24 1997-11-04 Marcade; Jean Paul Modular bifurcated intraluminal grafts and methods for delivering and assembling same
DE19508189C2 (en) * 1995-03-09 1998-07-02 Elco Europ Gmbh Electrical zero force contact plug device
WO1996032078A1 (en) 1995-04-14 1996-10-17 Schneider (Usa) Inc. Rolling membrane stent delivery device
US5591199A (en) 1995-06-07 1997-01-07 Porter; Christopher H. Curable fiber composite stent and delivery system
CA2179083A1 (en) 1995-08-01 1997-02-02 Michael S. Williams Composite metal and polymer locking stents for drug delivery
FI954565A0 (en) 1995-09-27 1995-09-27 Biocon Oy Biologically applied polymeric material to the implant and foil preparation
US5725517A (en) 1995-10-05 1998-03-10 Deroyal Industries, Inc. Absorbent woven article including radiopaque element woven therein and anchored at the ends thereof
US5762265A (en) * 1995-10-06 1998-06-09 Matsushita Electric Industrial Co., Ltd. Air-conditioning control unit
US5758562A (en) 1995-10-11 1998-06-02 Schneider (Usa) Inc. Process for manufacturing braided composite prosthesis
US5628788A (en) 1995-11-07 1997-05-13 Corvita Corporation Self-expanding endoluminal stent-graft
US5788626A (en) 1995-11-21 1998-08-04 Schneider (Usa) Inc Method of making a stent-graft covered with expanded polytetrafluoroethylene
US5946594A (en) * 1996-01-02 1999-08-31 Micron Technology, Inc. Chemical vapor deposition of titanium from titanium tetrachloride and hydrocarbon reactants
US5843158A (en) 1996-01-05 1998-12-01 Medtronic, Inc. Limited expansion endoluminal prostheses and methods for their use
JPH09215753A (en) * 1996-02-08 1997-08-19 Schneider Usa Inc Self-expanding stent made of titanium alloy
US5672877A (en) * 1996-03-27 1997-09-30 Adac Laboratories Coregistration of multi-modality data in a medical imaging system
US5824042A (en) * 1996-04-05 1998-10-20 Medtronic, Inc. Endoluminal prostheses having position indicating markers
US5718159A (en) * 1996-04-30 1998-02-17 Schneider (Usa) Inc. Process for manufacturing three-dimensional braided covered stent
US5670161A (en) 1996-05-28 1997-09-23 Healy; Kevin E. Biodegradable stent
FI105159B (en) 1996-10-25 2000-06-30 Biocon Ltd Surgical implant, agent or part thereof
US5718397A (en) * 1996-12-23 1998-02-17 Sonoco Products Company, Inc. Reel having concentric flange supports
US5741327A (en) * 1997-05-06 1998-04-21 Global Therapeutics, Inc. Surgical stent featuring radiopaque markers
US5980564A (en) * 1997-08-01 1999-11-09 Schneider (Usa) Inc. Bioabsorbable implantable endoprosthesis with reservoir
US6245103B1 (en) * 1997-08-01 2001-06-12 Schneider (Usa) Inc Bioabsorbable self-expanding stent
US20030204248A1 (en) * 2002-03-25 2003-10-30 Murphy Kieran P. Device viewable under an imaging beam

Patent Citations (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3918455A (en) * 1974-04-29 1975-11-11 Albany Int Corp Combined surgical suture and needle
US4471779A (en) * 1976-08-25 1984-09-18 Becton, Dickinson And Company Miniature balloon catheter
US5441517A (en) * 1991-11-08 1995-08-15 Kensey Nash Corporation Hemostatic puncture closure system and method of use
US5376376A (en) * 1992-01-13 1994-12-27 Li; Shu-Tung Resorbable vascular wound dressings
US5762625A (en) * 1992-09-08 1998-06-09 Kabushikikaisha Igaki Iryo Sekkei Luminal stent and device for inserting luminal stent
US5675146A (en) * 1992-09-25 1997-10-07 Texaco Inc. Naturally occurring radioactive material contamination detection means
US5628787A (en) * 1993-01-19 1997-05-13 Schneider (Usa) Inc. Clad composite stent
US5370691A (en) * 1993-01-26 1994-12-06 Target Therapeutics, Inc. Intravascular inflatable stent
US5632771A (en) * 1993-07-23 1997-05-27 Cook Incorporated Flexible stent having a pattern formed from a sheet of material
US5639777A (en) * 1993-11-30 1997-06-17 G.D. Searle & Co. 1,4,5-triphenyl pyrazolyl compounds for the treatment of inflammation and inflammation-related disorders
US5603722A (en) * 1995-06-06 1997-02-18 Quanam Medical Corporation Intravascular stent
US6174329B1 (en) * 1996-08-22 2001-01-16 Advanced Cardiovascular Systems, Inc. Protective coating for a stent with intermediate radiopaque coating
US5676146B1 (en) * 1996-09-13 2000-04-18 Osteotech Inc Surgical implant containing a resorbable radiopaque marker and method of locating such within a body
US5676146A (en) * 1996-09-13 1997-10-14 Osteotech, Inc. Surgical implant containing a resorbable radiopaque marker and method of locating such within a body
US5756127A (en) * 1996-10-29 1998-05-26 Wright Medical Technology, Inc. Implantable bioresorbable string of calcium sulfate beads
US5716397A (en) * 1996-12-06 1998-02-10 Medtronic, Inc. Annuloplasty device with removable stiffening element
US6174330B1 (en) * 1997-08-01 2001-01-16 Schneider (Usa) Inc Bioabsorbable marker having radiopaque constituents
US6340367B1 (en) * 1997-08-01 2002-01-22 Boston Scientific Scimed, Inc. Radiopaque markers and methods of using the same
US6626936B2 (en) * 1997-08-01 2003-09-30 Boston Scientific Scimed, Inc. Bioabsorbable marker having radiopaque constituents
US7083641B2 (en) * 1997-08-01 2006-08-01 Schneider (Usa) Inc. Radiopaque markers for implantable prostheses

Cited By (93)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090259125A1 (en) * 1997-08-01 2009-10-15 Boston Scientific Scimed, Inc. Bioabsorbable Marker Having Radiopaque Constituents And Method of Using the Same
US8668737B2 (en) 1997-10-10 2014-03-11 Senorx, Inc. Tissue marking implant
US8157862B2 (en) 1997-10-10 2012-04-17 Senorx, Inc. Tissue marking implant
US9039763B2 (en) 1997-10-10 2015-05-26 Senorx, Inc. Tissue marking implant
US9861294B2 (en) 1999-02-02 2018-01-09 Senorx, Inc. Marker delivery device with releasable plug
US9649093B2 (en) 1999-02-02 2017-05-16 Senorx, Inc. Cavity-filling biopsy site markers
US10172674B2 (en) 1999-02-02 2019-01-08 Senorx, Inc. Intracorporeal marker and marker delivery device
US8626270B2 (en) 1999-02-02 2014-01-07 Senorx, Inc. Cavity-filling biopsy site markers
US8224424B2 (en) 1999-02-02 2012-07-17 Senorx, Inc. Tissue site markers for in vivo imaging
US8498693B2 (en) 1999-02-02 2013-07-30 Senorx, Inc. Intracorporeal marker and marker delivery device
US8219182B2 (en) 1999-02-02 2012-07-10 Senorx, Inc. Cavity-filling biopsy site markers
US9820824B2 (en) 1999-02-02 2017-11-21 Senorx, Inc. Deployment of polysaccharide markers for treating a site within a patent
US8361082B2 (en) 1999-02-02 2013-01-29 Senorx, Inc. Marker delivery device with releasable plug
US8965486B2 (en) 1999-02-02 2015-02-24 Senorx, Inc. Cavity filling biopsy site markers
US9044162B2 (en) 1999-02-02 2015-06-02 Senorx, Inc. Marker delivery device with releasable plug
US9237937B2 (en) 1999-02-02 2016-01-19 Senorx, Inc. Cavity-filling biopsy site markers
US9149341B2 (en) 1999-02-02 2015-10-06 Senorx, Inc Deployment of polysaccharide markers for treating a site within a patient
US9579159B2 (en) 1999-06-17 2017-02-28 Bard Peripheral Vascular, Inc. Apparatus for the percutaneous marking of a lesion
US8579931B2 (en) 1999-06-17 2013-11-12 Bard Peripheral Vascular, Inc. Apparatus for the percutaneous marking of a lesion
US20040249436A1 (en) * 2000-05-19 2004-12-09 Aznoian Harold M. Stents and stenting methods
US8718745B2 (en) 2000-11-20 2014-05-06 Senorx, Inc. Tissue site markers for in vivo imaging
US8784433B2 (en) 2002-06-17 2014-07-22 Senorx, Inc. Plugged tip delivery tube for marker placement
US8177792B2 (en) 2002-06-17 2012-05-15 Senorx, Inc. Plugged tip delivery tube for marker placement
US10813716B2 (en) 2002-11-18 2020-10-27 Bard Peripheral Vascular, Inc. Self-contained, self-piercing, side-expelling marking apparatus
US9848956B2 (en) 2002-11-18 2017-12-26 Bard Peripheral Vascular, Inc. Self-contained, self-piercing, side-expelling marking apparatus
US10299881B2 (en) 2003-05-23 2019-05-28 Senorx, Inc. Marker or filler forming fluid
US8880154B2 (en) 2003-05-23 2014-11-04 Senorx, Inc. Fibrous marker and intracorporeal delivery thereof
US9801688B2 (en) 2003-05-23 2017-10-31 Senorx, Inc. Fibrous marker and intracorporeal delivery thereof
US8447386B2 (en) 2003-05-23 2013-05-21 Senorx, Inc. Marker or filler forming fluid
US8639315B2 (en) 2003-05-23 2014-01-28 Senorx, Inc. Marker or filler forming fluid
US10045832B2 (en) 2003-05-23 2018-08-14 Senorx, Inc. Marker or filler forming fluid
US8626269B2 (en) 2003-05-23 2014-01-07 Senorx, Inc. Fibrous marker and intracorporeal delivery thereof
US8634899B2 (en) 2003-11-17 2014-01-21 Bard Peripheral Vascular, Inc. Multi mode imaging marker
US10357328B2 (en) 2005-04-20 2019-07-23 Bard Peripheral Vascular, Inc. and Bard Shannon Limited Marking device with retractable cannula
US11278370B2 (en) 2005-04-20 2022-03-22 Bard Peripheral Vascular, Inc. Marking device with retractable cannula
US10342635B2 (en) 2005-04-20 2019-07-09 Bard Peripheral Vascular, Inc. Marking device with retractable cannula
US8353951B2 (en) * 2005-10-03 2013-01-15 Cardiatis S.A. Radio-opaque endoprosthesis
US20090192587A1 (en) * 2005-10-03 2009-07-30 Cardiatis S.A. Radio-opaque endoprosthesis
US8486028B2 (en) 2005-10-07 2013-07-16 Bard Peripheral Vascular, Inc. Tissue marking apparatus having drug-eluting tissue marker
US8361453B2 (en) * 2006-06-06 2013-01-29 Rutgers, The State University Of New Jersey Iodinated polymers
US20110022161A1 (en) * 2006-06-06 2011-01-27 Rutgers, The State University Of New Jersey Iodinated polymers
US20170035945A1 (en) * 2006-07-20 2017-02-09 Orbusneich Medical, Inc. Bioabsorbable polymeric composition for a medical device
US9642947B2 (en) * 2006-07-20 2017-05-09 Orbusneich Medical, Inc. Bioabsorbable polymeric composition for a medical device
US9642945B2 (en) * 2006-07-20 2017-05-09 Orbusneich Medical, Inc. Bioabsorbable polymeric composition for a medical device
US20170189585A1 (en) * 2006-07-20 2017-07-06 Orbusneich Medical, Inc. Bioabsorbable polymeric composition for a medical device
US20110034991A1 (en) * 2006-08-07 2011-02-10 Biotronik Vi Patent Ag Endoprosthesis and method for producing same
US20080097401A1 (en) * 2006-09-22 2008-04-24 Trapp Benjamin M Cerebral vasculature device
US9622770B2 (en) 2006-09-22 2017-04-18 W. L. Gore & Associates, Inc. Cerebral vasculature device
US8064987B2 (en) * 2006-10-23 2011-11-22 C. R. Bard, Inc. Breast marker
US20100030149A1 (en) * 2006-10-23 2010-02-04 C.R. Bard, Inc. Breast marker
US8437834B2 (en) 2006-10-23 2013-05-07 C. R. Bard, Inc. Breast marker
US8636787B2 (en) 2006-10-25 2014-01-28 Arterial Remodeling Technologies, S.A. Method for expansion and deployment of polymeric structures including stents
US20090099639A1 (en) * 2006-10-25 2009-04-16 Arterial Remodeling Technologies, S.A. Method for expansion and deployment of polymeric structures including stents
WO2008084286A3 (en) * 2006-10-25 2008-10-30 Arterial Remodeling Technologi Method for expansion and deployment of polymeric structures including stents
US9326869B2 (en) 2006-10-25 2016-05-03 Arterial Remodeling Technologies, S.A. Method for expansion and development of polymeric structures including stents
WO2008084286A2 (en) * 2006-10-25 2008-07-17 Arterial Remodeling Technologies, S.A. Method for expansion and deployment of polymeric structures including stents
US9901415B2 (en) 2006-12-12 2018-02-27 C. R. Bard, Inc. Multiple imaging mode tissue marker
US9579077B2 (en) 2006-12-12 2017-02-28 C.R. Bard, Inc. Multiple imaging mode tissue marker
US10682200B2 (en) 2006-12-12 2020-06-16 C. R. Bard, Inc. Multiple imaging mode tissue marker
US11471244B2 (en) 2006-12-12 2022-10-18 C.R. Bard, Inc. Multiple imaging mode tissue marker
US9042965B2 (en) 2006-12-18 2015-05-26 C. R. Bard, Inc. Biopsy marker with in situ-generated imaging properties
US8401622B2 (en) 2006-12-18 2013-03-19 C. R. Bard, Inc. Biopsy marker with in situ-generated imaging properties
US20080221670A1 (en) * 2007-03-07 2008-09-11 Claude Clerc Radiopaque polymeric stent
WO2008112076A1 (en) * 2007-03-07 2008-09-18 Boston Scientific Scimed, Inc. Radiopaque polymeric stent
US20100049302A1 (en) * 2007-03-14 2010-02-25 Sung-Gwon Kang Stent for expending intra luminal
US20100262182A1 (en) * 2007-05-15 2010-10-14 Occlutech Gmbh Occlusion Instruments Comprising Bioresorbable Radiopaque Polymeric Materials, As Well As Related Products, Methods And Uses
US8311610B2 (en) 2008-01-31 2012-11-13 C. R. Bard, Inc. Biopsy tissue marker
US20110166439A1 (en) * 2008-05-23 2011-07-07 Marvis Technologies Gmbh Medical instrument
US8579959B2 (en) 2008-09-12 2013-11-12 Cook Medical Technologies Llc Radiopaque reinforcing member
WO2010030370A1 (en) * 2008-09-12 2010-03-18 William A. Cook Australia Pty. Ltd. Radiopaque reinforcing member
US20110190868A1 (en) * 2008-09-12 2011-08-04 Werner Dieter Ducke Radiopaque reinforcing member
US11833275B2 (en) 2008-09-23 2023-12-05 Senorx, Inc. Porous bioabsorbable implant
US9327061B2 (en) 2008-09-23 2016-05-03 Senorx, Inc. Porous bioabsorbable implant
US10786604B2 (en) 2008-09-23 2020-09-29 Senorx, Inc. Porous bioabsorbable implant
US11779431B2 (en) 2008-12-30 2023-10-10 C. R. Bard, Inc. Marker delivery device for tissue marker placement
US10258428B2 (en) 2008-12-30 2019-04-16 C. R. Bard, Inc. Marker delivery device for tissue marker placement
US8670818B2 (en) 2008-12-30 2014-03-11 C. R. Bard, Inc. Marker delivery device for tissue marker placement
WO2012019090A1 (en) * 2010-08-05 2012-02-09 William A. Cook Australia Pty. Ltd. Stent graft having a marker and a reinforcing and marker ring
EP3378437A1 (en) * 2010-08-05 2018-09-26 Cook Medical Technologies LLC Stent graft having a marker and a reinforcing and marker ring
US20140094844A1 (en) * 2012-10-01 2014-04-03 Microvention, Inc Catheter Markers
US9504476B2 (en) * 2012-10-01 2016-11-29 Microvention, Inc. Catheter markers
US10806826B2 (en) 2013-01-09 2020-10-20 Bacterin International, Inc. Bone graft substitute containing a temporary contrast agent and a method of generating such and a method of use thereof
US9848883B2 (en) 2013-07-31 2017-12-26 EMBA Medical Limited Methods and devices for endovascular embolization
US10178995B2 (en) 2013-07-31 2019-01-15 NeuVT Limited Methods and devices for endovascular embolization
US10010328B2 (en) 2013-07-31 2018-07-03 NeuVT Limited Endovascular occlusion device with hemodynamically enhanced sealing and anchoring
US11517320B2 (en) 2013-07-31 2022-12-06 Embolic Acceleration, Llc Endovascular occlusion device with hemodynamically enhanced sealing and anchoring
US9681876B2 (en) 2013-07-31 2017-06-20 EMBA Medical Limited Methods and devices for endovascular embolization
USD715442S1 (en) 2013-09-24 2014-10-14 C. R. Bard, Inc. Tissue marker for intracorporeal site identification
USD715942S1 (en) 2013-09-24 2014-10-21 C. R. Bard, Inc. Tissue marker for intracorporeal site identification
USD716450S1 (en) 2013-09-24 2014-10-28 C. R. Bard, Inc. Tissue marker for intracorporeal site identification
USD716451S1 (en) 2013-09-24 2014-10-28 C. R. Bard, Inc. Tissue marker for intracorporeal site identification
EP4115854A1 (en) * 2015-01-12 2023-01-11 Microvention, Inc. Stent
US11696843B2 (en) 2015-01-12 2023-07-11 Microvention, Inc. Stent

Also Published As

Publication number Publication date
CA2238784C (en) 2003-08-05
DE69836656T3 (en) 2011-12-29
US20040111149A1 (en) 2004-06-10
ATE348638T1 (en) 2007-01-15
US20010021873A1 (en) 2001-09-13
JPH1157020A (en) 1999-03-02
EP0894503A3 (en) 2000-09-27
CA2238784A1 (en) 1999-02-01
JP4284427B2 (en) 2009-06-24
DE69836656D1 (en) 2007-02-01
EP0894503A2 (en) 1999-02-03
US6174330B1 (en) 2001-01-16
DE69836656T2 (en) 2007-09-27
US6626936B2 (en) 2003-09-30
ES2274556T3 (en) 2007-05-16
US20090259125A1 (en) 2009-10-15
US7553325B2 (en) 2009-06-30
EP0894503B1 (en) 2006-12-20
EP0894503B2 (en) 2011-04-13

Similar Documents

Publication Publication Date Title
US6626936B2 (en) Bioabsorbable marker having radiopaque constituents
US6340367B1 (en) Radiopaque markers and methods of using the same
EP2117463B1 (en) Radiopaque polymeric stent
US6585755B2 (en) Polymeric stent suitable for imaging by MRI and fluoroscopy
US20060276910A1 (en) Endoprostheses
AU762169B2 (en) Wire reinforced vascular prosthesis
JP2009514656A (en) Graft and stent graft with radiopaque beading
EP1295615A1 (en) Radiopaque stent
CN114652494A (en) Support frame
JP2023521091A (en) Self-expanding biodegradable stent braided with bioalloy

Legal Events

Date Code Title Description
AS Assignment

Owner name: BOSTON SCIENTIFIC SCIMED, INC., MINNESOTA

Free format text: CHANGE OF NAME;ASSIGNOR:SCIMED LIFE SYSTEMS, INC.;REEL/FRAME:018454/0866

Effective date: 20050101

Owner name: BOSTON SCIENTIFIC SCIMED, INC., MINNESOTA

Free format text: CHANGE OF NAME;ASSIGNOR:SCHNEIDER (USA) INC.;REEL/FRAME:018454/0858

Effective date: 19990427

Owner name: SCIMED LIFE SYSTEMS, INC., MINNESOTA

Free format text: MERGER;ASSIGNOR:BOSTON SCIENTIFIC SCIMED, INC.;REEL/FRAME:018454/0834

Effective date: 20050101

STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION

AS Assignment

Owner name: SCHNEIDER (USA) INC., MINNESOTA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:STINSON, JONATHAN S.;REEL/FRAME:025433/0516

Effective date: 19970731