WO1996034580A1 - Endoprosthesis for the treatment of blood-vessel bifurcation stenosis and purpose-built installation device - Google Patents

Endoprosthesis for the treatment of blood-vessel bifurcation stenosis and purpose-built installation device Download PDF

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Publication number
WO1996034580A1
WO1996034580A1 PCT/IB1996/000403 IB9600403W WO9634580A1 WO 1996034580 A1 WO1996034580 A1 WO 1996034580A1 IB 9600403 W IB9600403 W IB 9600403W WO 9634580 A1 WO9634580 A1 WO 9634580A1
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WO
WIPO (PCT)
Prior art keywords
balloon
fact
endoprosthesis
section
proximal
Prior art date
Application number
PCT/IB1996/000403
Other languages
French (fr)
Inventor
Alain Dibie
Original Assignee
Alain Dibie
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Alain Dibie filed Critical Alain Dibie
Priority to US08/945,973 priority Critical patent/US6183509B1/en
Priority to AT96910155T priority patent/ATE247436T1/en
Priority to DE69629599T priority patent/DE69629599T2/en
Priority to JP53315796A priority patent/JP3766977B2/en
Priority to EP96910155A priority patent/EP0957818B1/en
Priority to CA002220141A priority patent/CA2220141C/en
Priority to AU53450/96A priority patent/AU709513B2/en
Publication of WO1996034580A1 publication Critical patent/WO1996034580A1/en

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
    • A61F2/954—Instruments specially adapted for placement or removal of stents or stent-grafts for placing stents or stent-grafts in a bifurcation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
    • A61F2/958—Inflatable balloons for placing stents or stent-grafts
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06—Blood vessels
    • A61F2/07—Stent-grafts
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/856—Single tubular stent with a side portal passage
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06—Blood vessels
    • A61F2002/065—Y-shaped blood vessels
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
    • A61F2002/91533—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other characterised by the phase between adjacent bands
    • A61F2002/91541—Adjacent bands are arranged out of phase
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
    • A61F2002/9155—Adjacent bands being connected to each other
    • A61F2002/91558—Adjacent bands being connected to each other connected peak to peak
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
    • A61F2250/006—Additional features; Implant or prostheses properties not otherwise provided for modular

Definitions

  • This invention relates to the field of endoprostheses for the treatment of blood ⁇ vessel bifurcation stenosis.
  • This invention also relates to a purpose-built installation device.
  • endoprostheses formed from tubular structures perforated with a grid pattern of slits and consequently expandable following placement at the site of stenosis.
  • these endoprostheses are expanded by inflating a balloon which is placed inside them and subsequently withdrawn.
  • endoprostheses of this type may be said to have already given good service.
  • a primary goal of this invention is to develop existing endoprostheses in order to facilitate and improve treatment of blood-vessel bifurcation stenosis. This goal is attained by this invention through the use of an endoprosthesis comprising three tubular sections and two connectors, namely:
  • first distal section aligned at least approximately with the proximal section and intended for insertion into one of the vessels branching off from the bifurcation, this distal section being attached to the proximal section by means of a laterally positioned connector;
  • the two distal sections having their proximal ends joined by the second connector.
  • the distal end of the proximal section is chamfered and the proximal end of the second distal section is tapered at the other side of the second connector and fits into the chamfer in the proximal section.
  • the above-mentioned chamfered shapes and tapered ends may have a variety of embodiments. They may, in particular, be delimited by flat or curved surfaces.
  • Another important goal of this invention is to perfect the method of installing the above-mentioned endoprostheses.
  • first balloon of suitable length for insertion into two approximately aligned sections of the blood vessel to be treated: the main stem and the first branching blood vessel, on either side of the bifurcation area respectively;
  • the first balloon incorporates a lateral recess to be positioned facing the bifurcation area with a view to housing the proximal end of the second balloon.
  • the distal portion of the first balloon located downstream of the recess is of smaller diameter than the proximal portion of the balloon located upstream of the recess.
  • FIG. 1 is a schematic side view of an endoprosthesis in accordance with this invention
  • FIG. 1 is a perspective view of the same endoprosthesis
  • - figure 3 is another perspective view of the same endoprosthesis after relative inclination of the distal sections;
  • - figure 4 is a view of the same endoprosthesis following expansion of the various tubular sections from which it is formed;
  • - figure 5 is a schematic illustration of an endoprosthesis combined with the device for installing it, prior to implantation in a stenosis-affected bifurcation area;
  • - figure 6 is a view of the same instrument following implantation in a bifurcation and expansion of the proximal section and one distal section;
  • FIG. 7 is a view of the same endoprosthesis after expansion of the three sections from which it is formed;
  • - figure 8 is a schematic side view of the first balloon in accordance with the invention
  • - figure 9 is a side view of the second balloon in accordance with the invention
  • FIG. 10 is an overall view of an installation instrument comprising two balloons working together in accordance with the invention.
  • - figure 1 1 is another side view of the balloon-based installation system in accordance with the invention
  • - figure 12 is an overall view of the same balloon-based installation tool combined with means of inflation
  • FIG. 13 is a schematic cross-sectional view of a feeder tube for the double-balloon system.
  • endoprosthesis 100 comprises three tubular sections (1 10, 120 and 140) and two connectors (130 and 150).
  • the first section (1 10) is a proximal section having as its centre axis 1 1 1. It is intended for insertion into main stem Tl of blood vessel V for treatment, upstream of the bifurcation.
  • the first distal section (120) having as its section axis 121 is at least approximately aligned with proximal section 1 10 prior to use.
  • This first distal section 120 is intended for insertion into blood vessel T2 branching off from the bifurcation as is seen in particular in figures 6 and 7.
  • the first distal section (120) is attached to proximal section 1 10 by the first lateral connector (130).
  • the second distal section (140), having as its axis 141, is positioned at the side of the first distal section (120), and has the advantage of being parallel to the latter, prior to use.
  • the second distal section (140) is intended to be inserted into blood vessel T3 branching off from the bifurcation, as is seen in particular in figures 6 and 7.
  • the two distal sections 120 and 140 have their proximal ends (122 and 142) linked by the second connector (150).
  • Each of section 1 10, 120 and 140 is preferably formed from a tubular component perforated with a grid pattern of slits such that the structure of sections 1 10, 120 and 140 allows them to expand along their circumferences.
  • section 1 10, 120 and 140 of endoprosthesis 100 can be manufactured from extruded cylindrical parts made of a bendable metal alloy such as 316L stainless steel.
  • the external diameter of section of 1 10, 120 and 140 typically ranges from 1 to 1.2 mm prior to use:
  • the opening may take the form of a hexagon or diamond, as shown in the accompanying figures, taking on the appearance of grating following expansion against the inner surface of the coronary artery by means of a cylindrical balloon placed inside.
  • expandable tubular components 1 10, 120 and 140 and the material from which they are made are familiar to those skilled in the art, these particulars will not be described in detail in what follows.
  • the three sections 1 10, 120 and 140 are preferably of equal diameter prior to expansion, i.e. prior to use.
  • the respective axes (111, 121 and 141) of sections 1 10, 120 and 140 are coplanar and determine a plane of symmetry for the endoprosthesis. This plane of symmetry is parallel to the plane of figure 1.
  • the first connector (130) has as its centre the above-mentioned plane of symmetry determined by axes 1 1 1, 121 and 141.
  • Connector 130 links an area of distal end 1 13 of proximal section 1 10 with an area of proximal end 122 of the first distal section (120).
  • articulation 130 preferably consists of a strip of constant width parallel to axes 1 1 1 and 121. Articulation 130 is diametrically opposite the second distal section (140) with respect to axes 11 1 and 121.
  • proximal section 110 Distal end 113 of proximal section 110 is provided with chamfer 1 15 in its peripheral area situated opposite connector 130.
  • Chamfer 1 15 can be determined by a plane that is inclined with respect to axis 1 1 1, pe ⁇ endicular to the above-mentioned plane of symmetry or, again, be curved, for instance, concave with respect to distal section 120.
  • Angular opening of the wall of proximal section 1 10 thus increases starting from connector 130 and turns through 360°, i.e. a complete tubular form around axis 1 1 1.
  • This cant (1 15) forms a type of arch located on the side opposite connector 130 embodying in the cylindrical structure forming proximal section 1 10 the shape of the ostium of the blood vessel branching off from the coronary bifurcation onto which it will be applied.
  • proximal end 142 of the second distal section (140) is tapered at the other side of the second connector (150). It stretches forwards in its peripheral area opposite the second connector (150).
  • This tapered portion (144) may also be determined by a plane that is inclined with reference to axis 121, perpendicular to the plane of symmetry or, again, by a curved surface.
  • distal portion 1 13 with the corner cut off (1 15) of proximal section 1 10 is fixed together harmoniously with the proximal
  • the whole of the grid of the bifurcated endoprosthesis ( 100) covers the proximal and distal portions of the two coronary branching arteries and the whole of the dilated bifurcation area.
  • the first connector (130) preferably forms an integral part, i.e. it is not joined onto sections 1 10 and 120.
  • the first connector (130) and sections 110 and 120 are preferably manufactured from a single part in which connector 130 is formed via machining.
  • the second connector (150) is also centred with reference to the plane of symmetry determined by axes 1 1 1, 121 and 141. However, whereas the first connector (130) extends in a direction that is parallel to axes 11 1 and 121, the second connector (150) extends in a direction that is transversal to the above-mentioned axes 111, 121 and 141 and links adjacent areas of proximal ends 122 and 142 of distal sections 120 and 140.
  • the second connector (150) is preferably joined to proximal ends 122 and 142 of sections 120 and 140 by means of, for example, laser welding.
  • This aspect of the invention can, naturally, be embodied by a range of variants in that the second connector (150) could form an integral part with distal sections 120 and MO formed from a single part, while connector 130 would be joined by means of, for example, laser welding to the distal end of proximal section 1 10 and the proximal end of distal section 120.
  • bifurcated endoprosthesis 100 for the coronary artery conforming with this invention has the following dimensions:
  • the total length of endoprosthesis 100 measured from proximal end 1 12 of proximal section 1 10 to distal end 123 of distal section 120 is of the order of 15 mm;
  • proximal section 1 10 is of the order of 7.5 mm prior to expansion
  • distal section 120 is of the order of 7 mm prior to expansion
  • the length of distal section 140 is of the order of 9 mm prior to expansion;
  • the length of connector 130 is of the order of 0.5 to 1 mm;
  • this instrument (200) comprises two balloons (210 and 230).
  • the first balloon (210) is of a length consonant with its purpose of being positioned inside two approximately aligned sections (Tl and T2) of vessel V for treatment: main stem Tl and a branching vessel T2, situated one on either side of the bifurcation area respectively, or, again, of being positioned inside proximal section 1 10 and distal section 120 of endoprosthesis 100.
  • Balloon 230 is preferably shorter than balloon 210.
  • the two balloons 210 and 230 are preferably formed from generally cylindrical elongated tubular items centred upon axes 212 and 232 and having their ends (214 and 216; 234 and 236) more or less rounded.
  • the main balloon (210) preferably incorporates a recess in its side (218) suitable for housing proximal end 236 of the second balloon (230) as shown in figure 10.
  • proximal portion 219 of balloon 210 located upstream of recess 2 I S is preferably of greater diameter than distal portion 217 of the same balloon located downstream of recess 218.
  • Each of the balloons 210 and 230 is preferably fitted with a radio-opaque tracer
  • Tracers 220 and 240 are preferably located at the centres of their respective balloons 210 and 230. Tracers 220 and 240 may, for example, be carried by hollow internal tubes 221 and 241 housing metallic guides 222 and 242 having as their centres axes 212 and 232 and passing axially through balloons 210 and 230 respectively. Tracers 220 and 240 are preferably located halfway along balloons 210 and 230.
  • Balloons 210 and 230 are prolonged at their proximal ends 216 and 236 by, respectively, tubes 224 and 244, of narrow cross-section, designed to feed and, consequently, dilate balloons 210 and 230.
  • Tubes 224 and 244 preferably house guides 222 and 242. More specifically, each of the two tubes 224 and 244 preferably has two lumina: the first lumen houses a guide
  • the above-mentioned internal tubes 221 and 241 and first lumina are not connected with the internal surface of balloons 210 and 230.
  • internal tube 221 inside the first balloon (210) is preferably off-centre with respect to axis 212 in order to allow for the presence of recess 218 as is seen in figure S.
  • Inflation tubes 224 and 244 are joined at a certain distance from balloons 210 and 230 and are preferably attached by their proximal ends to a stiffer but both flexible and hollow common component 250 with two internal lumina (253 and 254) linked with inflation tubes 224 and 244 respectively or, more specifically, the said above-mentioned second inflation lumina of these tubes.
  • Component 250 is, moreover, itself fitted at its proximal end (252) with two connection systems with fluid sources linked with lumina 253 and 254 respectively, allowing balloons 210 and 230 to be expanded.
  • These connection systems may, for example, be of the type known as "Luer-Lock".
  • a variant on this is that the above-mentioned connection systems may be adapted to take a standard inflation syringe tip.
  • connection systems communicating with, respectively, lumina 253 and 254 formed inside component 250 should allow the two balloons (210 and 230) to be expanded separately.
  • Balloons 210 and 230 are preferably covered prior to use with a removable sheath (260).
  • Sheath 260 covers the full length of endoprosthesis 100, i.e. preferably a minimum of 15 to 20 mm.
  • Sheath 260 is preferably linked at its proximal end to a wire (262) facilitating removal of sheath 260 by pulling the said wire 262.
  • Wire 262 preferably passes through common tube 250.
  • Sheath 260 can, however, be omitted when the balloon system alone is used, i.e. without endoprosthesis 100.
  • the "Luer-Lock" connection systems shown in figure 12 are referred to as 252.
  • reference n° 270 in figure 12 labels a schematic inflation system comprising a pressure gauge (272) adapted for linkage to one of the connection system (252) with a view to dilating one of balloons 210 and 230.
  • Reference n° 253 and n° 254 in figure 13 label the two feeder lumina linking connection systems 252 with tubes 224 and 244 respectively.
  • reference ⁇ ° 255 in figure 13 labels the lumen housing the wire (262) facilitating the removal of sheath 260.
  • asymmetric double balloon 200 for coronary angioplasty conforming with this invention has the following dimensions:
  • - guide-wires 222 and 242 are 0.036 cm (0.014 inch) guide-wires
  • the longer balloon (210) is 20 to 25 mm in length, depending on the model;
  • - its proximal portion (219) is approximately 3.5 mm in diameter and approximately 6.5 mm in length after inflation;
  • - recess 21 S is approximately 3.5 mm in length;
  • - distal portion 217 is approximately 10 mm in length and approximately 3 mm in diameter after inflation;
  • - the second balloon (230) is approximately 13 mm in length and approximately 3 mm in diameter after inflation; - tubes 224 and 244 are joined approximately 10 mm from the proximal end (216) of balloon 210;
  • the lengths of the two tubes 224 and 244 between the point at which they join and common component 250 may range from approximately 20 to 30 cm;
  • the overall length, including balloons 210 and 230 and their feeder tubes is preferably approximately 135 mm;
  • the length of common tube 250 ranges from approximately 1 10 to 115 mm;
  • the outer diameter of the device with balloons 210 and 230 completely deflated preferably does not exceed 2 mm, so that the whole unit including the two balloons 210 and 230 and feeder tubes 224 and 244 may pass through an 8F guiding-catheter with an internal diameter of 2.6 mm.
  • the case is the same in the version of the balloon device fitted with endoprosthesis 100 and sheath 260.
  • the portion of tubes 224 and 244 that is located downstream of guide-wire exits 223 and 243 is preferably made of plastic.
  • the portion of tubes 224 and 244, including common portion 250, that is located upstream of exits 223 and 243 may be made of plastic or metal.
  • This tube (224, 244 and 250) must be as hydrophilic as possible in order to be able to slide inside its carrier catheter or guiding catheter.
  • balloons 210 and 230 are mutually independent. They are indirectly linked only in the area of common tube 250.
  • Guide-wires 222 and 242 preferably emerge from tubes 224 and 244 on the nearer side of common section 250, as is seen in figure 1 1. Exit points 223 and 243 of guide- ires 222 and 242 are preferably at a slight distance from each other and are marked differently for identification.
  • Balloons 210 and 230 located respectively inside proximal section 1 10 and distal section 120 in the case of balloon 210 and inside distal section 140 in the case of balloon 230, are still in a deflated state at this stage. Once it has been ascertained that sections 120 and 140 of the endoprosthesis have been correctly positioned at the bifurcation using radio-opaque tracers 220 and 240 contained in the balloons, the balloons can be inflated. To this end, the first asymmetric balloon (210), i.e.
  • the longer balloon which facilitates expansion of the main structure (110) of the endoprosthesis and of section 120, aligned with it is preferably inflated first.
  • balloon 210 thus increases proximal portion 110 of the endoprosthesis to 3.5 mm and distal portion 120 to 3 mm. This is followed by inflation of the shorter balloon (230), whose proximal end 236 fills recess 218 in balloon 210. Inflating balloon 230 thus dilates section 140 of the endoprosthesis.
  • proximal tapered shape of section 140 fits into the truncated form or form with its corner missing (115) of the main or proximal structure (1 10) of the endoprosthesis opposite and thus completely covers the ostial portion or bifurcation area of the coronary branching artery dilated and stented in the course of this procedure.
  • balloons 210 and 230 can be deflated and withdrawn.
  • Balloons 210 and 230 can be deflated and withdrawn simultaneously or separately, as appropriate, after being detached from the unit. It is advantageous for balloons 210 and 230 to be made from an elastic material manufactured from a plastic polymer.
  • the invention is not limited to dilation of a bifurcation area in a coronary artery showing a lesion at the bifurcation using endoprosthesis 100 and employing dilation of balloons 210 and 230.
  • the invention may also apply to other blood-vessel bifurcations, arteries or veins, such as, for example and non-limitatively, renal arteries, supra-aortic trunci, arteries leading from the aorta to the abdomen or to the low limbs, etc.
  • a particular variant of the invention is one in which balloon 210 may incorporate two portions (217 and 219), distal and proximal respectively, located on either side of recess 218 and having the same diameter. During deployment, balloon 230 may be inflated before balloon 210.
  • bifurcated endoprosthesis 100 may be envisaged using systems other than the double balloon structure illustrated in figures 8 et seqq., and, in a corollary manner, the double-balloon system (200) may be used as a double balloon for coronary bifurcation lesion arigioplasty not involving use of an endoprosthesis.
  • the first balloon 210 is symetric about its longitudinal axis 212.
  • the recess 218 is annular and symetric of revolution about this axis 212.

Abstract

This invention relates to an endoprosthesis for the treatment of blood-vessel bifurcation stenosis that is characterised by the fact that it comprises three tubular sections (110, 120 and 140) and two connectors (130 and 150), namely: a proximal section (110), a first distal section (120) aligned at least approximately with the proximal section (110) and intended for insertion into a first blood vessel (T2) branching off on the bifurcation, the first distal section (120) being linked to the proximal section (110) by a first lateral connector (130) and a second distal section (140), located at the side of the first distal section (120) and intended for insertion into a second vessel (T3) branching off from the bifurcation, the two distal sections (120 and 140) having their proximal ends linked by a second connector (150). The invention also relates to a double-balloon dilation system.

Description

ENDOPROSTHESIS FOR THE TREATMENT OF BLOOD-VESSEL BIFURCATION STENOSIS AND PURPOSE-BUILT INSTALLATION DEVICE
This invention relates to the field of endoprostheses for the treatment of blood¬ vessel bifurcation stenosis.
This invention also relates to a purpose-built installation device.
It has already been suggested that stenosis found in coronary arteries be treated using endoprostheses formed from tubular structures perforated with a grid pattern of slits and consequently expandable following placement at the site of stenosis. In most cases these endoprostheses are expanded by inflating a balloon which is placed inside them and subsequently withdrawn.
Generally speaking, endoprostheses of this type may be said to have already given good service.
They are not, however, fully satisfactory.
The applicant has, in particular, observed that standard endoprostheses are noi fully satisfactory when, as is frequently the case, there is stenosis at a blood-vessel bifurcation. In such cases, treatment using standard endoprostheses requires two separate endoprostheses. One of these is placed in each of the two vessels branching off from the bifurcation and their positioning in relation to each other is adjusted as finely as possible to ensure optimal cover of the bifurcation area.
A primary goal of this invention is to develop existing endoprostheses in order to facilitate and improve treatment of blood-vessel bifurcation stenosis. This goal is attained by this invention through the use of an endoprosthesis comprising three tubular sections and two connectors, namely:
- a proximal section;
- a first distal section aligned at least approximately with the proximal section and intended for insertion into one of the vessels branching off from the bifurcation, this distal section being attached to the proximal section by means of a laterally positioned connector; and
- a second distal section placed at the side of the first distal section and intended for insertion into the second vessel branching off from the bifurcation, the two distal sections having their proximal ends joined by the second connector. In accordance with another advantageous feature of this invention, the distal end of the proximal section is chamfered and the proximal end of the second distal section is tapered at the other side of the second connector and fits into the chamfer in the proximal section. The above-mentioned chamfered shapes and tapered ends may have a variety of embodiments. They may, in particular, be delimited by flat or curved surfaces.
Another important goal of this invention is to perfect the method of installing the above-mentioned endoprostheses.
According to this invention this goal is attained by using a double-balloon system, as follows:
- a first balloon of suitable length for insertion into two approximately aligned sections of the blood vessel to be treated: the main stem and the first branching blood vessel, on either side of the bifurcation area respectively; and
- a second balloon of suitable nature for insertion into the second blood vessel branching off from the bifurcation.
In accordance with another advantageous feature of the invention, the first balloon incorporates a lateral recess to be positioned facing the bifurcation area with a view to housing the proximal end of the second balloon.
In accordance with another advantageous feature of this invention, the distal portion of the first balloon located downstream of the recess is of smaller diameter than the proximal portion of the balloon located upstream of the recess.
Further features, goals and advantages of the invention will be apparent on reading the following detailed description as illustrated in the corresponding accompanying drawings, which are given as non-exhaustive examples and in which: - figure 1 is a schematic side view of an endoprosthesis in accordance with this invention;
- figure 2 is a perspective view of the same endoprosthesis;
- figure 3 is another perspective view of the same endoprosthesis after relative inclination of the distal sections; - figure 4 is a view of the same endoprosthesis following expansion of the various tubular sections from which it is formed;
- figure 5 is a schematic illustration of an endoprosthesis combined with the device for installing it, prior to implantation in a stenosis-affected bifurcation area; - figure 6 is a view of the same instrument following implantation in a bifurcation and expansion of the proximal section and one distal section;
- figure 7 is a view of the same endoprosthesis after expansion of the three sections from which it is formed;
- figure 8 is a schematic side view of the first balloon in accordance with the invention; - figure 9 is a side view of the second balloon in accordance with the invention;
- figure 10 is an overall view of an installation instrument comprising two balloons working together in accordance with the invention;
- figure 1 1 is another side view of the balloon-based installation system in accordance with the invention; - figure 12 is an overall view of the same balloon-based installation tool combined with means of inflation; and
- figure 13 is a schematic cross-sectional view of a feeder tube for the double-balloon system.
The first item described will be the structure of endoprosthesis 100 in accordance with the invention and illustrated in figures 1 to 7. As was mentioned earlier, endoprosthesis 100 comprises three tubular sections (1 10, 120 and 140) and two connectors (130 and 150).
The first section (1 10) is a proximal section having as its centre axis 1 1 1. It is intended for insertion into main stem Tl of blood vessel V for treatment, upstream of the bifurcation.
The first distal section (120) having as its section axis 121 is at least approximately aligned with proximal section 1 10 prior to use. This first distal section 120 is intended for insertion into blood vessel T2 branching off from the bifurcation as is seen in particular in figures 6 and 7. The first distal section (120) is attached to proximal section 1 10 by the first lateral connector (130).
The second distal section (140), having as its axis 141, is positioned at the side of the first distal section (120), and has the advantage of being parallel to the latter, prior to use. The second distal section (140) is intended to be inserted into blood vessel T3 branching off from the bifurcation, as is seen in particular in figures 6 and 7.
The two distal sections 120 and 140 have their proximal ends (122 and 142) linked by the second connector (150).
Each of section 1 10, 120 and 140 is preferably formed from a tubular component perforated with a grid pattern of slits such that the structure of sections 1 10, 120 and 140 allows them to expand along their circumferences.
In practice, section 1 10, 120 and 140 of endoprosthesis 100 can be manufactured from extruded cylindrical parts made of a bendable metal alloy such as 316L stainless steel. The external diameter of section of 1 10, 120 and 140 typically ranges from 1 to 1.2 mm prior to use:
There can be a range of variants of the grid pattern cut into sections 1 10, 120 and 140. The opening may take the form of a hexagon or diamond, as shown in the accompanying figures, taking on the appearance of grating following expansion against the inner surface of the coronary artery by means of a cylindrical balloon placed inside. As the basic structure of expandable tubular components 1 10, 120 and 140 and the material from which they are made are familiar to those skilled in the art, these particulars will not be described in detail in what follows.
The three sections 1 10, 120 and 140 are preferably of equal diameter prior to expansion, i.e. prior to use. The respective axes (111, 121 and 141) of sections 1 10, 120 and 140 are coplanar and determine a plane of symmetry for the endoprosthesis. This plane of symmetry is parallel to the plane of figure 1.
The first connector (130) has as its centre the above-mentioned plane of symmetry determined by axes 1 1 1, 121 and 141. Connector 130 links an area of distal end 1 13 of proximal section 1 10 with an area of proximal end 122 of the first distal section (120). Yet more specifically, articulation 130 preferably consists of a strip of constant width parallel to axes 1 1 1 and 121. Articulation 130 is diametrically opposite the second distal section (140) with respect to axes 11 1 and 121.
Distal end 113 of proximal section 110 is provided with chamfer 1 15 in its peripheral area situated opposite connector 130. Chamfer 1 15 can be determined by a plane that is inclined with respect to axis 1 1 1, peφendicular to the above-mentioned plane of symmetry or, again, be curved, for instance, concave with respect to distal section 120. Angular opening of the wall of proximal section 1 10 thus increases starting from connector 130 and turns through 360°, i.e. a complete tubular form around axis 1 1 1.
This cant (1 15) forms a type of arch located on the side opposite connector 130 embodying in the cylindrical structure forming proximal section 1 10 the shape of the ostium of the blood vessel branching off from the coronary bifurcation onto which it will be applied.
Furthermore, proximal end 142 of the second distal section (140) is tapered at the other side of the second connector (150). It stretches forwards in its peripheral area opposite the second connector (150). This tapered portion (144) may also be determined by a plane that is inclined with reference to axis 121, perpendicular to the plane of symmetry or, again, by a curved surface.
After expansion, as is illustrated in figure 4 for example, when the endoprosthesis is installed at the bifurcation of the two coronary arteries, distal portion 1 13 with the corner cut off (1 15) of proximal section 1 10 is fixed together harmoniously with the proximal
(144) of section 140 of the endoprosthesis and ensures maximum coverage of the dilated coronary bifurcation area.
In this way, once in place, the whole of the grid of the bifurcated endoprosthesis ( 100) covers the proximal and distal portions of the two coronary branching arteries and the whole of the dilated bifurcation area.
The first connector (130) preferably forms an integral part, i.e. it is not joined onto sections 1 10 and 120. In other words, the first connector (130) and sections 110 and 120 are preferably manufactured from a single part in which connector 130 is formed via machining.
The second connector (150) is also centred with reference to the plane of symmetry determined by axes 1 1 1, 121 and 141. However, whereas the first connector (130) extends in a direction that is parallel to axes 11 1 and 121, the second connector (150) extends in a direction that is transversal to the above-mentioned axes 111, 121 and 141 and links adjacent areas of proximal ends 122 and 142 of distal sections 120 and 140.
The second connector (150) is preferably joined to proximal ends 122 and 142 of sections 120 and 140 by means of, for example, laser welding.
This aspect of the invention can, naturally, be embodied by a range of variants in that the second connector (150) could form an integral part with distal sections 120 and MO formed from a single part, while connector 130 would be joined by means of, for example, laser welding to the distal end of proximal section 1 10 and the proximal end of distal section 120.
In accordance with a particular embodiment, given as a non-exhaustive example, bifurcated endoprosthesis 100 for the coronary artery conforming with this invention has the following dimensions:
- the total length of endoprosthesis 100 measured from proximal end 1 12 of proximal section 1 10 to distal end 123 of distal section 120 is of the order of 15 mm;
- the diameter of sections 1 10, 120 and 140 is of the order of 1 mm prior to expansion;
- the length of proximal section 1 10 is of the order of 7.5 mm prior to expansion;
- the length of distal section 120 is of the order of 7 mm prior to expansion;
- the length of distal section 140 is of the order of 9 mm prior to expansion; - the length of connector 130 is of the order of 0.5 to 1 mm; and
- the diameter of distal sections 120 and 140 in their expanded state is of the order of 3 mm while the diameter of proximal section 1 10 is of the order of 3.5 mm A description now follows of the structure of the instrument fitted with a double asymmetric balloon conforming with this invention which is shown in figure 8 et seqq.
Essentially, this instrument (200) comprises two balloons (210 and 230). The first balloon (210) is of a length consonant with its purpose of being positioned inside two approximately aligned sections (Tl and T2) of vessel V for treatment: main stem Tl and a branching vessel T2, situated one on either side of the bifurcation area respectively, or, again, of being positioned inside proximal section 1 10 and distal section 120 of endoprosthesis 100.
As regards the second balloon (230), this is consonant with its puφose of being positioned in the second blood vessel (T3) branching off from the bifurcation. Balloon 230 is preferably shorter than balloon 210. As shown in the accompanying figures, the two balloons 210 and 230 are preferably formed from generally cylindrical elongated tubular items centred upon axes 212 and 232 and having their ends (214 and 216; 234 and 236) more or less rounded. The main balloon (210) preferably incorporates a recess in its side (218) suitable for housing proximal end 236 of the second balloon (230) as shown in figure 10.
Furthermore, proximal portion 219 of balloon 210 located upstream of recess 2 I S is preferably of greater diameter than distal portion 217 of the same balloon located downstream of recess 218. Each of the balloons 210 and 230 is preferably fitted with a radio-opaque tracer
(220 and 240). Tracers 220 and 240 are preferably located at the centres of their respective balloons 210 and 230. Tracers 220 and 240 may, for example, be carried by hollow internal tubes 221 and 241 housing metallic guides 222 and 242 having as their centres axes 212 and 232 and passing axially through balloons 210 and 230 respectively. Tracers 220 and 240 are preferably located halfway along balloons 210 and 230.
Balloons 210 and 230 are prolonged at their proximal ends 216 and 236 by, respectively, tubes 224 and 244, of narrow cross-section, designed to feed and, consequently, dilate balloons 210 and 230. Tubes 224 and 244 preferably house guides 222 and 242. More specifically, each of the two tubes 224 and 244 preferably has two lumina: the first lumen houses a guide
(222 and 242) and opens into the associated internal tube (221 and 241) and the second lumen, used for inflating the balloons, opens into the inside surface of the balloons (210 and 230).
The above-mentioned internal tubes 221 and 241 and first lumina are not connected with the internal surface of balloons 210 and 230.
Furthermore, internal tube 221 inside the first balloon (210) is preferably off-centre with respect to axis 212 in order to allow for the presence of recess 218 as is seen in figure S.
Inflation tubes 224 and 244 are joined at a certain distance from balloons 210 and 230 and are preferably attached by their proximal ends to a stiffer but both flexible and hollow common component 250 with two internal lumina (253 and 254) linked with inflation tubes 224 and 244 respectively or, more specifically, the said above-mentioned second inflation lumina of these tubes. Component 250 is, moreover, itself fitted at its proximal end (252) with two connection systems with fluid sources linked with lumina 253 and 254 respectively, allowing balloons 210 and 230 to be expanded. These connection systems may, for example, be of the type known as "Luer-Lock". A variant on this is that the above-mentioned connection systems may be adapted to take a standard inflation syringe tip.
It is important that the above-mentioned connection systems communicating with, respectively, lumina 253 and 254 formed inside component 250 should allow the two balloons (210 and 230) to be expanded separately.
Balloons 210 and 230 are preferably covered prior to use with a removable sheath (260). Sheath 260 covers the full length of endoprosthesis 100, i.e. preferably a minimum of 15 to 20 mm. Sheath 260 is preferably linked at its proximal end to a wire (262) facilitating removal of sheath 260 by pulling the said wire 262. Wire 262 preferably passes through common tube 250.
Sheath 260 can, however, be omitted when the balloon system alone is used, i.e. without endoprosthesis 100. The "Luer-Lock" connection systems shown in figure 12 are referred to as 252. Furthermore, reference n° 270 in figure 12 labels a schematic inflation system comprising a pressure gauge (272) adapted for linkage to one of the connection system (252) with a view to dilating one of balloons 210 and 230. Reference n° 253 and n° 254 in figure 13 label the two feeder lumina linking connection systems 252 with tubes 224 and 244 respectively. In addition, reference π° 255 in figure 13 labels the lumen housing the wire (262) facilitating the removal of sheath 260.
In accordance with a particular embodiment that is, naturally, non-exhaustive, asymmetric double balloon 200 for coronary angioplasty conforming with this invention has the following dimensions:
- guide-wires 222 and 242 are 0.036 cm (0.014 inch) guide-wires;
- the longer balloon (210) is 20 to 25 mm in length, depending on the model;
- its proximal portion (219) is approximately 3.5 mm in diameter and approximately 6.5 mm in length after inflation; - recess 21 S is approximately 3.5 mm in length;
- distal portion 217 is approximately 10 mm in length and approximately 3 mm in diameter after inflation;
- the second balloon (230) is approximately 13 mm in length and approximately 3 mm in diameter after inflation; - tubes 224 and 244 are joined approximately 10 mm from the proximal end (216) of balloon 210;
- the lengths of the two tubes 224 and 244 between the point at which they join and common component 250 may range from approximately 20 to 30 cm;
- the overall length, including balloons 210 and 230 and their feeder tubes is preferably approximately 135 mm;
- the length of common tube 250 ranges from approximately 1 10 to 115 mm; and
- the outer diameter of the device with balloons 210 and 230 completely deflated preferably does not exceed 2 mm, so that the whole unit including the two balloons 210 and 230 and feeder tubes 224 and 244 may pass through an 8F guiding-catheter with an internal diameter of 2.6 mm. The case is the same in the version of the balloon device fitted with endoprosthesis 100 and sheath 260. The portion of tubes 224 and 244 that is located downstream of guide-wire exits 223 and 243 is preferably made of plastic.
The portion of tubes 224 and 244, including common portion 250, that is located upstream of exits 223 and 243 may be made of plastic or metal. This tube (224, 244 and 250) must be as hydrophilic as possible in order to be able to slide inside its carrier catheter or guiding catheter.
It should be noted that balloons 210 and 230 are mutually independent. They are indirectly linked only in the area of common tube 250.
Guide-wires 222 and 242 preferably emerge from tubes 224 and 244 on the nearer side of common section 250, as is seen in figure 1 1. Exit points 223 and 243 of guide- ires 222 and 242 are preferably at a slight distance from each other and are marked differently for identification.
A description now follows of the process for installing endoprosthesis 100 using asymmetric double balloon 200 in accordance with this invention. Prior to use, the unit combining the two balloons (210 and 230) and bifurcated endoprosthesis 100 is protected by covering sheath 260. This unit fitted with sheath 260 is firstly manoeuvred close to the bifurcation stenosis area. Its position is monitored using radio-opaque tracers 220 and 240.
Once the balloon (210 and 230) / endoprosthesis ( 100) unit has arrived at the bifurcation, above-mentioned sheath 260 can be withdrawn by pulling wire 262.
After protective sheath 260 has been withdrawn, guide-wires 222 and 242, which have been inserted into blood vessels T2 and T3 branching off from the coronary bifurcation, are manipulated. Balloons 210 and 230, located respectively inside proximal section 1 10 and distal section 120 in the case of balloon 210 and inside distal section 140 in the case of balloon 230, are still in a deflated state at this stage. Once it has been ascertained that sections 120 and 140 of the endoprosthesis have been correctly positioned at the bifurcation using radio-opaque tracers 220 and 240 contained in the balloons, the balloons can be inflated. To this end, the first asymmetric balloon (210), i.e. the longer balloon which facilitates expansion of the main structure (110) of the endoprosthesis and of section 120, aligned with it, is preferably inflated first. Typically balloon 210 thus increases proximal portion 110 of the endoprosthesis to 3.5 mm and distal portion 120 to 3 mm. This is followed by inflation of the shorter balloon (230), whose proximal end 236 fills recess 218 in balloon 210. Inflating balloon 230 thus dilates section 140 of the endoprosthesis. The proximal tapered shape of section 140 fits into the truncated form or form with its corner missing (115) of the main or proximal structure (1 10) of the endoprosthesis opposite and thus completely covers the ostial portion or bifurcation area of the coronary branching artery dilated and stented in the course of this procedure.
Once the bifurcated endoprosthesis has been deployed and installed, as shown in figure 7, balloons 210 and 230 can be deflated and withdrawn.
Balloons 210 and 230 can be deflated and withdrawn simultaneously or separately, as appropriate, after being detached from the unit. It is advantageous for balloons 210 and 230 to be made from an elastic material manufactured from a plastic polymer.
This invention is not, of course, restricted to the particular embodiment described above but stems to any and all variants consistent with the idea embodied.
In particular, the invention is not limited to dilation of a bifurcation area in a coronary artery showing a lesion at the bifurcation using endoprosthesis 100 and employing dilation of balloons 210 and 230. The invention may also apply to other blood-vessel bifurcations, arteries or veins, such as, for example and non-limitatively, renal arteries, supra-aortic trunci, arteries leading from the aorta to the abdomen or to the low limbs, etc.
A particular variant of the invention is one in which balloon 210 may incorporate two portions (217 and 219), distal and proximal respectively, located on either side of recess 218 and having the same diameter. During deployment, balloon 230 may be inflated before balloon 210.
Furthermore, installation and dilation of bifurcated endoprosthesis 100 may be envisaged using systems other than the double balloon structure illustrated in figures 8 et seqq., and, in a corollary manner, the double-balloon system (200) may be used as a double balloon for coronary bifurcation lesion arigioplasty not involving use of an endoprosthesis.
According to a variant of the invention, the first balloon 210 is symetric about its longitudinal axis 212. In other words the recess 218 is annular and symetric of revolution about this axis 212.

Claims

1. An endoprosthesis for the treatment of blood-vessel bifurcation stenosis characterised by its comprising three tubular sections (1 10, 120 and 140) and two connectors (130 and 150), namely:
- a proximal section (1 10);
- a distal section (120) aligned at least approximately with the proximal section (1 10) and intended for insertion into one of the blood vessels (T2) branching off from the bifurcation, the distal section (1 10) being linked to the proximal section (110) by a lateral connector (130); and
- a second distal section (140) located at the side of the first distal section (120) and intended for insertion into the second blood vessel (T3) branching off from the bifurcation, both distal sections (120 and 140) having their proximal ends linked by a second connector ( 150).
2. An endoprosthesis, as claimed in Claim 1, characterised by the fact that the distal end (1 13) of the proximal section (1 10) is chamfered and the proximal end (142) of the second distal section (140) is tapered at the other side of the second connector ( 150) and able to fit into the chamfered form (1 15) of the proximal section (1 10).
3. An endoprosthesis, as claimed in Claim 2, characterised by the fact that the chamfer form (1 15) and/or the tapered section (144) is delimited by a flat surface.
4. An endoprosthesis, as claimed in Claim 2, characterised by the fact that the chamfer form (1 15) and/or the tapered section (144) is delimited by a curved surface.
5. An endoprosthesis, as claimed in one of Claims 1 to 4, characterised by the fact that the three tubular sections (1 10, 120 and 140) are of identical diameter prior to use.
6. An endoprosthesis, as claimed in one of Claims 1 to 5, characterised by the fact that the first connector (130) has at its centre a plane of symmetry determined by the axes (1 1 1, 121 and 141) of the tubular sections and extends in a direction that is approximately parallel to these axes.
7. An endoprosthesis, as claimed in one of Claims 1 to 6, characterised by the fact that the first connector (130) is formed from the same part as the proximal section (1 10) and the first distal section (120).
8. An endoprosthesis, as claimed in one of Claims 1 to 7, characterised by the fact that the second connector (150) has as its centre a plane of symmetry determined by the axes (1 1 1, 121 and 141) of the tubular sections and extends in a direction approximately perpendicular to these axes.
9. An endoprosthesis, as claimed in one of Claims 1 to 8, characterised by the fact that the second connector (150) is attached to the two distal sections (120 and 140).
10. An endoprosthesis, as claimed in one of Claims 1 to 9, characterised by the fact that each of the sections (1 10, 120 and 140) is formed from a tubular component with a grid pattern of slits susceptible of expansion circumferentially.
1 1. A balloon system for dilating blood vessels characterised by the fact that it comprises a double balloon, namely: - one balloon (210) of suitable length for being positioned in two approximately aligned sections (T 1 and T2) for the vessel for treatment: a main stem (T 1 ) and a branching vessel
(V2), located one on each side of the bifurcation area; and
- a second balloon (230) suitable for positioning in the second blood vessel (T3) branching off from the bifurcation.
12. A system, as claimed in Claim 1 1, characterised by the fact that the first balloon (210) incorporates a lateral recess (218) intended for positioning opposite the bifurcation area in order to house the proximal end (236) of the second balloon (320).
13. A system, as claimed in one of Claims 1 1 and 12, characterised by the fact that the proximal portion (219) of the first balloon (210) located upstream of the recess (218) is of greater diameter than the distal portion (217) of the same balloon located downstream of the recess.
14. A system, as claimed in one of Claims 1 1 to 13, characterised by the fact that each balloon has a radio-opaque tracer (220 and 240).
15. A system, as claimed in one of Claims 1 1 to 14, characterised by the fact that the two balloons (210 and 230) are placed in a removable sheath (260) combined with a manoeuvring wire (262). 15
16. A system, as claimed in one of Claims 11 to 15, characterised by the fact that each balloon (210 and 230) has an inflation tube (224 and 244) protruding from its proximal end.
17. A system, as claimed in Claim 16, characterised by the fact that the two inflation tubes (224 and 244) are joined to a common component (250) comprising two lumina at a certain distance from the proximal end of the balloons (210 and 230).
18. A system, as claimed in one of Claims 11 to 17, characterised by the fact that each balloon (210 and 230) is combined with a guide (121 and 141).
19. A system, as claimed in one of Claims 11 to 18, characterised by the fact that the second balloon (230) is shorter than the first balloon (210).
20. The use of the system consistent with one of Claims 1 1 to 19 for dilation of an endoprosthesis consonant with one of Claims 1 to 10.
21. The use of the system consistent with one of Claims 1 1 to 19 for bifurcation lesion angioplasty.
PCT/IB1996/000403 1995-05-04 1996-05-03 Endoprosthesis for the treatment of blood-vessel bifurcation stenosis and purpose-built installation device WO1996034580A1 (en)

Priority Applications (7)

Application Number Priority Date Filing Date Title
US08/945,973 US6183509B1 (en) 1995-05-04 1996-05-03 Endoprosthesis for the treatment of blood-vessel bifurcation stenosis and purpose-built installation device
AT96910155T ATE247436T1 (en) 1995-05-04 1996-05-03 ENDOPROSTHESIS FOR THE TREATMENT OF BIFURCATION STENOSIS IN BLOOD VESSELS
DE69629599T DE69629599T2 (en) 1995-05-04 1996-05-03 ENDOPROTHESIS FOR TREATING BIFURCATION STENOSES IN BLOOD VESSELS
JP53315796A JP3766977B2 (en) 1995-05-04 1996-05-03 Endoprosthesis for the treatment of vascular stenosis and its mounting device
EP96910155A EP0957818B1 (en) 1995-05-04 1996-05-03 Endoprosthesis for the treatment of blood-vessel bifurcation stenosis
CA002220141A CA2220141C (en) 1995-05-04 1996-05-03 Endoprosthesis for the treatment of blood-vessel bifurcation stenosis and purpose-built installation device
AU53450/96A AU709513B2 (en) 1995-05-04 1996-05-03 Endoprosthesis for the treatment of blood-vessel bifurcation stenosis and purpose-built installation device

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
FR9505334A FR2733682B1 (en) 1995-05-04 1995-05-04 ENDOPROSTHESIS FOR THE TREATMENT OF STENOSIS ON BIFURCATIONS OF BLOOD VESSELS AND LAYING EQUIPMENT THEREFOR
FR95/05334 1995-05-04

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WO1996034580A1 true WO1996034580A1 (en) 1996-11-07

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US (3) US6183509B1 (en)
EP (1) EP0957818B1 (en)
JP (1) JP3766977B2 (en)
AT (1) ATE247436T1 (en)
AU (1) AU709513B2 (en)
CA (1) CA2220141C (en)
DE (1) DE69629599T2 (en)
ES (1) ES2205022T3 (en)
FR (1) FR2733682B1 (en)
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Cited By (72)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE29701758U1 (en) * 1997-02-01 1997-03-27 Jomed Implantate Gmbh Radially expandable stent for implantation in a body vessel, particularly in the area of a vascular branch
DE29708803U1 (en) * 1997-05-17 1997-07-31 Jomed Implantate Gmbh Radially expandable stent for implantation in a body vessel in the area of a vascular branch
WO1997041803A1 (en) * 1996-05-03 1997-11-13 Divysio Solutions Ulc. Bifurcated stent and method for the manufacture of same
US5755734A (en) * 1996-05-03 1998-05-26 Medinol Ltd. Bifurcated stent and method of making same
WO1998031303A1 (en) * 1997-01-16 1998-07-23 Medicorp R & D Benelux S.A. Luminal endoprosthesis for ramification
WO1998037833A1 (en) * 1997-02-25 1998-09-03 Symbiotech Medical, Inc. Expandable intravascular stent
EP0891751A1 (en) * 1997-07-18 1999-01-20 Thomas Prof. Dr. Ischinger Vascular stent for bifurcations, sidebranches and ostial lesions and an application catheter and method for implantation
EP0893107A1 (en) * 1996-02-21 1999-01-27 Robert E. Fischell Expandable stent
WO1999004726A1 (en) * 1997-07-28 1999-02-04 Marco Zimarino Expandable bifurcated stent
EP0897700A1 (en) * 1997-08-13 1999-02-24 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
EP0916317A1 (en) * 1997-11-13 1999-05-19 Medinol Ltd. Multilayered metal stent
WO1999044539A2 (en) * 1998-03-05 1999-09-10 Scimed Life Systems, Inc. Dilatation and stent delivery system for bifurcation lesions
US5961490A (en) * 1995-08-29 1999-10-05 Scimed Life Systems, Inc. Balloon perfusion catheter
EP0956832A1 (en) * 1998-05-05 1999-11-17 Medinol Ltd. Bifurcated stent with improved side branch aperture and method of making same
WO1999066861A1 (en) * 1998-06-25 1999-12-29 Patrice Bergeron System for three-dimensional positioning of instruments by intraluminal tract
US6017363A (en) * 1997-09-22 2000-01-25 Cordis Corporation Bifurcated axially flexible stent
WO2000010489A1 (en) * 1998-08-24 2000-03-02 Advanced Cardiovascular Systems, Inc. Bifurcated catheter assembly
US6096073A (en) * 1997-02-25 2000-08-01 Scimed Life Systems, Inc. Method of deploying a stent at a lesion site located at a bifurcation in a parent vessel
EP1047356A1 (en) † 1998-01-14 2000-11-02 Advanced Stent Technologies, Inc. Extendible stent apparatus
US6143002A (en) * 1998-08-04 2000-11-07 Scimed Life Systems, Inc. System for delivering stents to bifurcation lesions
US6190403B1 (en) 1998-11-13 2001-02-20 Cordis Corporation Low profile radiopaque stent with increased longitudinal flexibility and radial rigidity
WO2001043665A2 (en) * 1999-12-10 2001-06-21 Advanced Cardiovascular Systems, Inc. Bifurcated stent delivery system having retractable sheath
WO2001074273A1 (en) * 2000-03-30 2001-10-11 Advanced Cardiovascular Systems, Inc. Bifurcated stent system
AU747698B2 (en) * 1997-09-23 2002-05-16 Design & Performance - Cyprus Limited Bifurcated stent with flexible side portion
EP1151730A3 (en) * 2000-05-02 2002-06-12 Cordis Corporation Bifurcated stent and stent delivery system
US6436104B2 (en) 1996-01-26 2002-08-20 Cordis Corporation Bifurcated axially flexible stent
US6514281B1 (en) 1998-09-04 2003-02-04 Scimed Life Systems, Inc. System for delivering bifurcation stents
AU769241B2 (en) * 1996-05-03 2004-01-22 Evysio Medical Devices Ulc Bifurcated stent and method for the manufacture of same
US6740114B2 (en) 2001-03-01 2004-05-25 Cordis Corporation Flexible stent
US6746476B1 (en) 1997-09-22 2004-06-08 Cordis Corporation Bifurcated axially flexible stent
US6770092B2 (en) 1996-05-03 2004-08-03 Medinol Ltd. Method of delivering a bifurcated stent
US6790227B2 (en) 2001-03-01 2004-09-14 Cordis Corporation Flexible stent
EP1512380A1 (en) * 1999-06-04 2005-03-09 Advanced Stent Technologies, Inc. Stent delivery system for branched vessel
US6989026B2 (en) 1996-05-03 2006-01-24 Medinol Ltd. Method of making a bifurcated stent with improved side branch aperture
US7018400B2 (en) * 1997-09-24 2006-03-28 Medtronic Vascular, Inc. Endolumenal prothesis and method of use in bifurcation regions of body lumens
WO2007002423A2 (en) * 2005-06-24 2007-01-04 Abbott Laboratories Balloon catheter
EP1804879A2 (en) * 2004-09-24 2007-07-11 FlowMedica, Inc. Systems and methods for bi-lateral guidewire cannulation of branched body lumens
WO2008024943A1 (en) * 2006-08-23 2008-02-28 Abbott Laboratories Catheter system and method for delivering medical devices
US7465315B2 (en) 2003-11-19 2008-12-16 Advanced Cardiovascular Systems, Inc. Portal design for stent for treating bifurcated vessels
US7476243B2 (en) 1999-01-27 2009-01-13 Boston Scientific Scimed, Inc. Bifurcation stent delivery system
US7540879B2 (en) 2000-02-18 2009-06-02 E.V.R. Endovascular Researches S.A. Endolumenal device for delivering and deploying an endolumenal expandable prosthesis
US7641685B2 (en) 1996-05-03 2010-01-05 Medinol Ltd. System and method for delivering a bifurcated stent
US7686845B2 (en) * 2000-05-30 2010-03-30 Devax, Inc. Noncylindrical stent deployment system for treating vascular bifurcations
US7862609B2 (en) 2000-11-16 2011-01-04 Cordis Corporation Stent graft having a pleated graft member
US7955379B2 (en) * 1997-08-13 2011-06-07 Abbott Cardiovascular Systems Inc. Stent and catheter assembly and method for treating bifurcations
US8182527B2 (en) 2001-05-07 2012-05-22 Cordis Corporation Heparin barrier coating for controlled drug release
US8231667B2 (en) 2002-11-08 2012-07-31 Jacques Séguin Endoprosthesis for vascular bifurcation
US8236048B2 (en) 2000-05-12 2012-08-07 Cordis Corporation Drug/drug delivery systems for the prevention and treatment of vascular disease
US8337540B2 (en) * 2001-05-17 2012-12-25 Advanced Cardiovascular Systems, Inc. Stent for treating bifurcations and method of use
US8728143B2 (en) 1996-06-06 2014-05-20 Biosensors International Group, Ltd. Endoprosthesis deployment system for treating vascular bifurcations
EP2744457A1 (en) * 2011-08-19 2014-06-25 Al-saadon, Khalid Stent system, deployment apparatus and method for bifurcated lesion
US8834554B2 (en) 2006-08-22 2014-09-16 Abbott Cardiovascular Systems Inc. Intravascular stent
US8882826B2 (en) 2006-08-22 2014-11-11 Abbott Cardiovascular Systems Inc. Intravascular stent
US8932340B2 (en) 2008-05-29 2015-01-13 Boston Scientific Scimed, Inc. Bifurcated stent and delivery system
US8945202B2 (en) 2009-04-28 2015-02-03 Endologix, Inc. Fenestrated prosthesis
EP1905398B1 (en) 1998-01-14 2015-05-13 Advanced Stent Technologies, Inc. Extendible stent apparatus
US9101501B2 (en) 1996-06-06 2015-08-11 Biosensors International Group, Ltd. Bifurcation stent and method of positioning in a body lumen
US9393100B2 (en) 2010-11-17 2016-07-19 Endologix, Inc. Devices and methods to treat vascular dissections
US9427340B2 (en) 2004-12-14 2016-08-30 Boston Scientific Scimed, Inc. Stent with protruding branch portion for bifurcated vessels
US9492297B2 (en) 2006-09-12 2016-11-15 Boston Scientific Scimed, Inc. Multilayer balloon for bifurcated stent delivery and methods of making and using the same
US9549835B2 (en) 2011-03-01 2017-01-24 Endologix, Inc. Catheter system and methods of using same
US9561126B2 (en) 1996-11-04 2017-02-07 Boston Scientific Scimed, Inc. Catheter with attached flexible side sheath
US9579103B2 (en) 2009-05-01 2017-02-28 Endologix, Inc. Percutaneous method and device to treat dissections
US9700701B2 (en) 2008-07-01 2017-07-11 Endologix, Inc. Catheter system and methods of using same
US9757262B2 (en) 2009-07-15 2017-09-12 Endologix, Inc. Stent graft
US9907642B2 (en) 2009-07-27 2018-03-06 Endologix, Inc. Stent graft
US10245166B2 (en) 2008-02-22 2019-04-02 Endologix, Inc. Apparatus and method of placement of a graft or graft system
US10314700B2 (en) 2007-02-05 2019-06-11 Boston Scientific Scimed, Inc. Synthetic composite structures
WO2020053144A1 (en) * 2018-09-11 2020-03-19 Car Holding B.V. Kissing balloons
US10772717B2 (en) 2009-05-01 2020-09-15 Endologix, Inc. Percutaneous method and device to treat dissections
US11129737B2 (en) 2015-06-30 2021-09-28 Endologix Llc Locking assembly for coupling guidewire to delivery system
US11406518B2 (en) 2010-11-02 2022-08-09 Endologix Llc Apparatus and method of placement of a graft or graft system

Families Citing this family (215)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6039749A (en) 1994-02-10 2000-03-21 Endovascular Systems, Inc. Method and apparatus for deploying non-circular stents and graftstent complexes
US6258116B1 (en) * 1996-01-26 2001-07-10 Cordis Corporation Bifurcated axially flexible stent
US6599316B2 (en) * 1996-11-04 2003-07-29 Advanced Stent Technologies, Inc. Extendible stent apparatus
US7220275B2 (en) * 1996-11-04 2007-05-22 Advanced Stent Technologies, Inc. Stent with protruding branch portion for bifurcated vessels
US6835203B1 (en) * 1996-11-04 2004-12-28 Advanced Stent Technologies, Inc. Extendible stent apparatus
US7341598B2 (en) 1999-01-13 2008-03-11 Boston Scientific Scimed, Inc. Stent with protruding branch portion for bifurcated vessels
US6596020B2 (en) * 1996-11-04 2003-07-22 Advanced Stent Technologies, Inc. Method of delivering a stent with a side opening
AU4896797A (en) * 1996-11-04 1998-05-29 Davidson, Charles Extendible stent apparatus and method for deploying the same
US7591846B2 (en) * 1996-11-04 2009-09-22 Boston Scientific Scimed, Inc. Methods for deploying stents in bifurcations
US6325826B1 (en) 1998-01-14 2001-12-04 Advanced Stent Technologies, Inc. Extendible stent apparatus
US6951572B1 (en) * 1997-02-20 2005-10-04 Endologix, Inc. Bifurcated vascular graft and method and apparatus for deploying same
US6070589A (en) 1997-08-01 2000-06-06 Teramed, Inc. Methods for deploying bypass graft stents
US6254627B1 (en) * 1997-09-23 2001-07-03 Diseno Y Desarrollo Medico S.A. De C.V. Non-thrombogenic stent jacket
US6887268B2 (en) * 1998-03-30 2005-05-03 Cordis Corporation Extension prosthesis for an arterial repair
US6290731B1 (en) 1998-03-30 2001-09-18 Cordis Corporation Aortic graft having a precursor gasket for repairing an abdominal aortic aneurysm
US6093203A (en) * 1998-05-13 2000-07-25 Uflacker; Renan Stent or graft support structure for treating bifurcated vessels having different diameter portions and methods of use and implantation
WO1999065419A1 (en) 1998-06-19 1999-12-23 Endologix, Inc. Self expanding bifurcated endovascular prosthesis
US8257425B2 (en) * 1999-01-13 2012-09-04 Boston Scientific Scimed, Inc. Stent with protruding branch portion for bifurcated vessels
US20050060027A1 (en) * 1999-01-13 2005-03-17 Advanced Stent Technologies, Inc. Catheter balloon systems and methods
US7655030B2 (en) 2003-07-18 2010-02-02 Boston Scientific Scimed, Inc. Catheter balloon systems and methods
US8034100B2 (en) * 1999-03-11 2011-10-11 Endologix, Inc. Graft deployment system
US6261316B1 (en) 1999-03-11 2001-07-17 Endologix, Inc. Single puncture bifurcation graft deployment system
US7387639B2 (en) * 1999-06-04 2008-06-17 Advanced Stent Technologies, Inc. Short sleeve stent delivery catheter and methods
CN1409622A (en) * 1999-09-23 2003-04-09 先进扩张技术公司 Bifurcation stent system and method
US6689156B1 (en) * 1999-09-23 2004-02-10 Advanced Stent Technologies, Inc. Stent range transducers and methods of use
US6361555B1 (en) 1999-12-15 2002-03-26 Advanced Cardiovascular Systems, Inc. Stent and stent delivery assembly and method of use
US6468301B1 (en) * 2000-03-27 2002-10-22 Aga Medical Corporation Repositionable and recapturable vascular stent/graft
US20030139803A1 (en) * 2000-05-30 2003-07-24 Jacques Sequin Method of stenting a vessel with stent lumenal diameter increasing distally
US20020072792A1 (en) * 2000-09-22 2002-06-13 Robert Burgermeister Stent with optimal strength and radiopacity characteristics
WO2002039888A2 (en) * 2000-11-15 2002-05-23 Endologix, Inc. Implantable vascular graft
US7314483B2 (en) * 2000-11-16 2008-01-01 Cordis Corp. Stent graft with branch leg
US20070168006A1 (en) * 2001-02-20 2007-07-19 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20070173911A1 (en) * 2001-02-20 2007-07-26 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US6829509B1 (en) * 2001-02-20 2004-12-07 Biophan Technologies, Inc. Electromagnetic interference immune tissue invasive system
US20050288750A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050283167A1 (en) * 2003-08-25 2005-12-22 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050283214A1 (en) * 2003-08-25 2005-12-22 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20070168005A1 (en) * 2001-02-20 2007-07-19 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050288753A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
WO2002067815A1 (en) 2001-02-26 2002-09-06 Scimed Life Systems, Inc. Bifurcated stent
WO2002067816A1 (en) * 2001-02-26 2002-09-06 Scimed Life Systems, Inc. Bifurcated stent and delivery system
WO2002067653A2 (en) * 2001-02-26 2002-09-06 Scimed Life Systems, Inc. Bifurcated stent and delivery system
US6676691B1 (en) * 2001-03-28 2004-01-13 Ayman A. Hosny Stent delivery system
US20050021123A1 (en) * 2001-04-30 2005-01-27 Jurgen Dorn Variable speed self-expanding stent delivery system and luer locking connector
US20040176837A1 (en) * 2001-05-17 2004-09-09 Atladottir Svava Maria Self-expanding stent and catheter assembly and method for treating bifurcations
US6749628B1 (en) 2001-05-17 2004-06-15 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US8617231B2 (en) 2001-05-18 2013-12-31 Boston Scientific Scimed, Inc. Dual guidewire exchange catheter system
US6712844B2 (en) 2001-06-06 2004-03-30 Advanced Cardiovascular Systems, Inc. MRI compatible stent
AU2002315223A1 (en) * 2001-06-19 2003-01-02 Eva Corporation Positioning apparatus for use in repairing a vessel
GB0121980D0 (en) 2001-09-11 2001-10-31 Cathnet Science Holding As Expandable stent
US7182779B2 (en) * 2001-12-03 2007-02-27 Xtent, Inc. Apparatus and methods for positioning prostheses for deployment from a catheter
US20030135266A1 (en) * 2001-12-03 2003-07-17 Xtent, Inc. Apparatus and methods for delivery of multiple distributed stents
US7309350B2 (en) * 2001-12-03 2007-12-18 Xtent, Inc. Apparatus and methods for deployment of vascular prostheses
US20050121411A1 (en) * 2002-10-29 2005-06-09 Microfabrica Inc. Medical devices and EFAB methods and apparatus for producing them
US7137993B2 (en) 2001-12-03 2006-11-21 Xtent, Inc. Apparatus and methods for delivery of multiple distributed stents
US7892273B2 (en) * 2001-12-03 2011-02-22 Xtent, Inc. Custom length stent apparatus
US7351255B2 (en) * 2001-12-03 2008-04-01 Xtent, Inc. Stent delivery apparatus and method
US8080048B2 (en) * 2001-12-03 2011-12-20 Xtent, Inc. Stent delivery for bifurcated vessels
US7294146B2 (en) 2001-12-03 2007-11-13 Xtent, Inc. Apparatus and methods for delivery of variable length stents
US20040186551A1 (en) 2003-01-17 2004-09-23 Xtent, Inc. Multiple independent nested stent structures and methods for their preparation and deployment
US7147656B2 (en) * 2001-12-03 2006-12-12 Xtent, Inc. Apparatus and methods for delivery of braided prostheses
US7147661B2 (en) 2001-12-20 2006-12-12 Boston Scientific Santa Rosa Corp. Radially expandable stent
GB0206061D0 (en) * 2002-03-14 2002-04-24 Angiomed Ag Metal structure compatible with MRI imaging, and method of manufacturing such a structure
US6802859B1 (en) * 2002-07-12 2004-10-12 Endovascular Technologies, Inc. Endovascular stent-graft with flexible bifurcation
US6761734B2 (en) * 2002-07-22 2004-07-13 William S. Suhr Segmented balloon catheter for stenting bifurcation lesions
US20050065596A1 (en) * 2002-07-24 2005-03-24 Xufan Tseng Stents capable of controllably releasing histone deacetylase inhibitors
US7942920B2 (en) * 2003-02-25 2011-05-17 Cordis Corporation Stent with nested fingers for enhanced vessel coverage
US7918884B2 (en) * 2003-02-25 2011-04-05 Cordis Corporation Stent for treatment of bifurcated lesions
US20050131524A1 (en) * 2003-02-25 2005-06-16 Majercak David C. Method for treating a bifurcated vessel
US7758630B2 (en) * 2003-04-14 2010-07-20 Tryton Medical, Inc. Helical ostium support for treating vascular bifurcations
US7972372B2 (en) * 2003-04-14 2011-07-05 Tryton Medical, Inc. Kit for treating vascular bifurcations
US7731747B2 (en) * 2003-04-14 2010-06-08 Tryton Medical, Inc. Vascular bifurcation prosthesis with multiple thin fronds
US7717953B2 (en) * 2004-10-13 2010-05-18 Tryton Medical, Inc. Delivery system for placement of prosthesis at luminal OS
US8109987B2 (en) 2003-04-14 2012-02-07 Tryton Medical, Inc. Method of treating a lumenal bifurcation
US8083791B2 (en) * 2003-04-14 2011-12-27 Tryton Medical, Inc. Method of treating a lumenal bifurcation
US7481834B2 (en) * 2003-04-14 2009-01-27 Tryton Medical, Inc. Stent for placement at luminal os
US7241308B2 (en) * 2003-06-09 2007-07-10 Xtent, Inc. Stent deployment systems and methods
US7959665B2 (en) * 2003-07-31 2011-06-14 Abbott Cardiovascular Systems Inc. Intravascular stent with inverted end rings
US20050050042A1 (en) * 2003-08-20 2005-03-03 Marvin Elder Natural language database querying
US8298280B2 (en) * 2003-08-21 2012-10-30 Boston Scientific Scimed, Inc. Stent with protruding branch portion for bifurcated vessels
US20050283213A1 (en) * 2003-08-25 2005-12-22 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050288754A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US7344559B2 (en) * 2003-08-25 2008-03-18 Biophan Technologies, Inc. Electromagnetic radiation transparent device and method of making thereof
US8868212B2 (en) * 2003-08-25 2014-10-21 Medtronic, Inc. Medical device with an electrically conductive anti-antenna member
US20050288752A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050288756A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050080475A1 (en) * 2003-10-14 2005-04-14 Xtent, Inc. A Delaware Corporation Stent delivery devices and methods
US7553324B2 (en) * 2003-10-14 2009-06-30 Xtent, Inc. Fixed stent delivery devices and methods
US7344557B2 (en) * 2003-11-12 2008-03-18 Advanced Stent Technologies, Inc. Catheter balloon systems and methods
WO2005058202A1 (en) * 2003-12-17 2005-06-30 Cook Incorporated Interconnected leg extensions for an endoluminal prostehsis
US20070156225A1 (en) * 2003-12-23 2007-07-05 Xtent, Inc. Automated control mechanisms and methods for custom length stent apparatus
US7326236B2 (en) 2003-12-23 2008-02-05 Xtent, Inc. Devices and methods for controlling and indicating the length of an interventional element
US8007528B2 (en) * 2004-03-17 2011-08-30 Boston Scientific Scimed, Inc. Bifurcated stent
US7323006B2 (en) * 2004-03-30 2008-01-29 Xtent, Inc. Rapid exchange interventional devices and methods
US7674284B2 (en) * 2004-03-31 2010-03-09 Cook Incorporated Endoluminal graft
US20050228477A1 (en) * 2004-04-09 2005-10-13 Xtent, Inc. Topographic coatings and coating methods for medical devices
CA2559540A1 (en) 2004-06-08 2005-12-29 Advanced Stent Technologies, Inc. Stent with protruding branch portion for bifurcated vessels
US8317859B2 (en) 2004-06-28 2012-11-27 J.W. Medical Systems Ltd. Devices and methods for controlling expandable prostheses during deployment
US20050288766A1 (en) * 2004-06-28 2005-12-29 Xtent, Inc. Devices and methods for controlling expandable prostheses during deployment
US20060064064A1 (en) * 2004-09-17 2006-03-23 Jang G D Two-step/dual-diameter balloon angioplasty catheter for bifurcation and side-branch vascular anatomy
US20060069424A1 (en) * 2004-09-27 2006-03-30 Xtent, Inc. Self-constrained segmented stents and methods for their deployment
US20060089704A1 (en) * 2004-10-25 2006-04-27 Myles Douglas Vascular graft and deployment system
US7699883B2 (en) * 2004-10-25 2010-04-20 Myles Douglas Vascular graft and deployment system
US7588596B2 (en) * 2004-12-29 2009-09-15 Scimed Life Systems, Inc. Endoluminal prosthesis adapted to resist migration and method of deploying the same
US20070150051A1 (en) * 2005-01-10 2007-06-28 Duke Fiduciary, Llc Vascular implants and methods of fabricating the same
US8287583B2 (en) * 2005-01-10 2012-10-16 Taheri Laduca Llc Apparatus and method for deploying an implantable device within the body
US8128680B2 (en) 2005-01-10 2012-03-06 Taheri Laduca Llc Apparatus and method for deploying an implantable device within the body
US20060155366A1 (en) * 2005-01-10 2006-07-13 Laduca Robert Apparatus and method for deploying an implantable device within the body
US20080188803A1 (en) * 2005-02-03 2008-08-07 Jang G David Triple-profile balloon catheter
US7850645B2 (en) * 2005-02-11 2010-12-14 Boston Scientific Scimed, Inc. Internal medical devices for delivery of therapeutic agent in conjunction with a source of electrical power
US7402168B2 (en) * 2005-04-11 2008-07-22 Xtent, Inc. Custom-length stent delivery system with independently operable expansion elements
US20070010736A1 (en) * 2005-05-19 2007-01-11 Biophan Technologies, Inc. Electromagnetic resonant circuit sleeve for implantable medical device
US8317855B2 (en) * 2005-05-26 2012-11-27 Boston Scientific Scimed, Inc. Crimpable and expandable side branch cell
US20060271161A1 (en) * 2005-05-26 2006-11-30 Boston Scientific Scimed, Inc. Selective treatment of stent side branch petals
US8480728B2 (en) * 2005-05-26 2013-07-09 Boston Scientific Scimed, Inc. Stent side branch deployment initiation geometry
DE602005025035D1 (en) * 2005-06-29 2011-01-05 Bipin C Patadia SYSTEM FOR STORING A PROXIMALLY INCREASED STENT
DE202005012982U1 (en) * 2005-08-17 2005-10-27 Odu-Steckverbindungssysteme Gmbh & Co. Kg In line electrical connector has a plug with spring arm formed lugs that latch into holes in socket body to secure
ATE526911T1 (en) 2005-08-17 2011-10-15 Bard Inc C R VARIABLE SPEED STENT DELIVERY SYSTEM
US8038706B2 (en) * 2005-09-08 2011-10-18 Boston Scientific Scimed, Inc. Crown stent assembly
US7731741B2 (en) 2005-09-08 2010-06-08 Boston Scientific Scimed, Inc. Inflatable bifurcation stent
US8043366B2 (en) * 2005-09-08 2011-10-25 Boston Scientific Scimed, Inc. Overlapping stent
CA2623254A1 (en) * 2005-09-21 2007-03-29 B-Balloon Ltd. Bifurcated balloon and stent
US20070106375A1 (en) * 2005-11-07 2007-05-10 Carlos Vonderwalde Bifurcated stent assembly
US8192477B2 (en) * 2005-11-14 2012-06-05 Boston Scientific Scimed, Inc. Twisting bifurcation delivery system
US20070112418A1 (en) 2005-11-14 2007-05-17 Boston Scientific Scimed, Inc. Stent with spiral side-branch support designs
US8343211B2 (en) * 2005-12-14 2013-01-01 Boston Scientific Scimed, Inc. Connectors for bifurcated stent
US8435284B2 (en) * 2005-12-14 2013-05-07 Boston Scientific Scimed, Inc. Telescoping bifurcated stent
US7540881B2 (en) 2005-12-22 2009-06-02 Boston Scientific Scimed, Inc. Bifurcation stent pattern
CA2936205C (en) * 2006-01-13 2018-08-21 C.R. Bard, Inc. Stent delivery system
US11026822B2 (en) 2006-01-13 2021-06-08 C. R. Bard, Inc. Stent delivery system
US20070168013A1 (en) * 2006-01-19 2007-07-19 Myles Douglas Vascular graft and deployment system
US20070179587A1 (en) * 2006-01-30 2007-08-02 Xtent, Inc. Apparatus and methods for deployment of custom-length prostheses
US8821561B2 (en) * 2006-02-22 2014-09-02 Boston Scientific Scimed, Inc. Marker arrangement for bifurcation catheter
US8926679B2 (en) 2006-03-03 2015-01-06 Boston Scientific Scimed, Inc. Bifurcated stent system balloon folds
US7833264B2 (en) * 2006-03-06 2010-11-16 Boston Scientific Scimed, Inc. Bifurcated stent
US20070208414A1 (en) * 2006-03-06 2007-09-06 Shawn Sorenson Tapered strength rings on a bifurcated stent petal
US20070208411A1 (en) * 2006-03-06 2007-09-06 Boston Scientific Scimed, Inc. Bifurcated stent with surface area gradient
US20070208419A1 (en) * 2006-03-06 2007-09-06 Boston Scientific Scimed, Inc. Bifurcation stent with uniform side branch projection
US8298278B2 (en) * 2006-03-07 2012-10-30 Boston Scientific Scimed, Inc. Bifurcated stent with improvement securement
US8167929B2 (en) * 2006-03-09 2012-05-01 Abbott Laboratories System and method for delivering a stent to a bifurcated vessel
US20070260224A1 (en) * 2006-03-09 2007-11-08 Abbott Laboratories Flexible catheter tip having a shaped head
US20070270933A1 (en) * 2006-03-09 2007-11-22 Abbott Laboratories Stent having contoured proximal end
US8257419B2 (en) * 2006-03-10 2012-09-04 Cordis Corporation Apparatus for treating a bifurcated region of a conduit
JP2009530060A (en) 2006-03-20 2009-08-27 エックステント・インコーポレーテッド Apparatus and method for deploying connected prosthetic segments
US20070233233A1 (en) * 2006-03-31 2007-10-04 Boston Scientific Scimed, Inc Tethered expansion columns for controlled stent expansion
US20070260304A1 (en) * 2006-05-02 2007-11-08 Daniel Gregorich Bifurcated stent with minimally circumferentially projected side branch
US7537608B2 (en) * 2006-05-23 2009-05-26 Boston Scientific Scimed, Inc. Stent with variable crimping diameter
US20070281117A1 (en) * 2006-06-02 2007-12-06 Xtent, Inc. Use of plasma in formation of biodegradable stent coating
KR100728253B1 (en) * 2006-06-07 2007-06-13 고충원 Stent for branch blood vessel and balloon catheter comprising the same
EP2051673A2 (en) 2006-06-23 2009-04-29 Boston Scientific Limited Bifurcated stent with twisted hinges
US8029558B2 (en) * 2006-07-07 2011-10-04 Abbott Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
GB0615658D0 (en) * 2006-08-07 2006-09-13 Angiomed Ag Hand-held actuator device
US20080269865A1 (en) * 2006-08-07 2008-10-30 Xtent, Inc. Custom Length Stent Apparatus
DE102006039236A1 (en) * 2006-08-21 2008-02-28 Variomed Ag Apparatus and method for reducing or removing stenoses
US8177829B2 (en) * 2006-08-23 2012-05-15 Boston Scientific Scimed, Inc. Auxiliary balloon catheter
US20080071343A1 (en) * 2006-09-15 2008-03-20 Kevin John Mayberry Multi-segmented graft deployment system
US7951191B2 (en) 2006-10-10 2011-05-31 Boston Scientific Scimed, Inc. Bifurcated stent with entire circumferential petal
US8206429B2 (en) 2006-11-02 2012-06-26 Boston Scientific Scimed, Inc. Adjustable bifurcation catheter incorporating electroactive polymer and methods of making and using the same
US7842082B2 (en) 2006-11-16 2010-11-30 Boston Scientific Scimed, Inc. Bifurcated stent
US8768486B2 (en) * 2006-12-11 2014-07-01 Medtronic, Inc. Medical leads with frequency independent magnetic resonance imaging protection
US8216298B2 (en) 2007-01-05 2012-07-10 Medtronic Vascular, Inc. Branch vessel graft method and delivery system
US8523931B2 (en) * 2007-01-12 2013-09-03 Endologix, Inc. Dual concentric guidewire and methods of bifurcated graft deployment
US7959668B2 (en) * 2007-01-16 2011-06-14 Boston Scientific Scimed, Inc. Bifurcated stent
EP2111190B1 (en) 2007-01-19 2013-10-09 Medtronic, Inc. Stented heart valve devices for atrioventricular valve replacement
BRPI0807261B8 (en) 2007-02-09 2021-06-22 Taheri Laduca Llc stent-loaded catheter sets
JP2010517703A (en) * 2007-02-09 2010-05-27 タヘリ ラドュカ エルエルシー Vascular graft and method for processing the same
US20080199510A1 (en) * 2007-02-20 2008-08-21 Xtent, Inc. Thermo-mechanically controlled implants and methods of use
US20090131868A1 (en) * 2007-03-20 2009-05-21 Das Gladwin S Balloon catheters and related methods
US8486132B2 (en) 2007-03-22 2013-07-16 J.W. Medical Systems Ltd. Devices and methods for controlling expandable prostheses during deployment
US8118861B2 (en) * 2007-03-28 2012-02-21 Boston Scientific Scimed, Inc. Bifurcation stent and balloon assemblies
US8647376B2 (en) * 2007-03-30 2014-02-11 Boston Scientific Scimed, Inc. Balloon fold design for deployment of bifurcated stent petal architecture
US20090012601A1 (en) * 2007-07-05 2009-01-08 Abbott Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
GB0713497D0 (en) 2007-07-11 2007-08-22 Angiomed Ag Device for catheter sheath retraction
US8486134B2 (en) 2007-08-01 2013-07-16 Boston Scientific Scimed, Inc. Bifurcation treatment system and methods
US7959669B2 (en) 2007-09-12 2011-06-14 Boston Scientific Scimed, Inc. Bifurcated stent with open ended side branch support
US20090076584A1 (en) * 2007-09-19 2009-03-19 Xtent, Inc. Apparatus and methods for deployment of multiple custom-length prostheses
US20090125097A1 (en) * 2007-11-13 2009-05-14 Medtronic Vascular, Inc. Device and Method for Stent Graft Fenestration in Situ
US8936567B2 (en) * 2007-11-14 2015-01-20 Boston Scientific Scimed, Inc. Balloon bifurcated lumen treatment
US7833266B2 (en) 2007-11-28 2010-11-16 Boston Scientific Scimed, Inc. Bifurcated stent with drug wells for specific ostial, carina, and side branch treatment
US8277501B2 (en) 2007-12-21 2012-10-02 Boston Scientific Scimed, Inc. Bi-stable bifurcated stent petal geometry
WO2009088953A2 (en) * 2007-12-31 2009-07-16 Boston Scientific Scimed Inc. Bifurcation stent delivery system and methods
US9101503B2 (en) * 2008-03-06 2015-08-11 J.W. Medical Systems Ltd. Apparatus having variable strut length and methods of use
US8236040B2 (en) 2008-04-11 2012-08-07 Endologix, Inc. Bifurcated graft deployment systems and methods
US8377108B2 (en) 2008-06-02 2013-02-19 Boston Scientific Scimed, Inc. Staggered two balloon bifurcation catheter assembly and methods
JP5662310B2 (en) * 2008-06-05 2015-01-28 ボストン サイエンティフィック サイムド，インコーポレイテッドＢｏｓｔｏｎ Ｓｃｉｅｎｔｉｆｉｃ Ｓｃｉｍｅｄ，Ｉｎｃ． Shrinkable branch device and method of manufacturing the same
US8398697B2 (en) * 2008-06-13 2013-03-19 Boston Scientific Scimed, Inc. Bifurcation catheter assembly with distally mounted side balloon and methods
US8163123B2 (en) * 2008-07-31 2012-04-24 Boston Scientific Scimed, Inc. Bifurcation catheter dual balloon bond and methods
US20100049307A1 (en) * 2008-08-25 2010-02-25 Aga Medical Corporation Stent graft having extended landing area and method for using the same
US8133199B2 (en) 2008-08-27 2012-03-13 Boston Scientific Scimed, Inc. Electroactive polymer activation system for a medical device
US8769796B2 (en) 2008-09-25 2014-07-08 Advanced Bifurcation Systems, Inc. Selective stent crimping
US8795347B2 (en) 2008-09-25 2014-08-05 Advanced Bifurcation Systems, Inc. Methods and systems for treating a bifurcation with provisional side branch stenting
US8821562B2 (en) 2008-09-25 2014-09-02 Advanced Bifurcation Systems, Inc. Partially crimped stent
US11298252B2 (en) 2008-09-25 2022-04-12 Advanced Bifurcation Systems Inc. Stent alignment during treatment of a bifurcation
CN102215780B (en) 2008-09-25 2015-10-14 高级分支系统股份有限公司 Part crimped stent
US8292941B2 (en) * 2009-04-23 2012-10-23 Medtronic Vascular, Inc. Delivery system for deployment of a one-piece iliac-branch device
KR101073035B1 (en) * 2009-05-13 2011-10-12 연세대학교 산학협력단 H Side-branch Stent
US20100318170A1 (en) * 2009-06-15 2010-12-16 Richard Newhauser Proximal catheter flap for managing wire twist
US20100331960A1 (en) * 2009-06-30 2010-12-30 Boston Scientific Scimed, Inc. Endoprosthesis and endoprosthesis delivery system and method
US8382818B2 (en) * 2009-07-02 2013-02-26 Tryton Medical, Inc. Ostium support for treating vascular bifurcations
EP2477558B1 (en) 2009-09-14 2016-08-10 CircuLite, Inc. Endovascular anastomotic connector device and delivery system
US20110218617A1 (en) * 2010-03-02 2011-09-08 Endologix, Inc. Endoluminal vascular prosthesis
CA2794080A1 (en) 2010-03-24 2011-09-29 Advanced Bifurcation Systems, Inc. System and methods for treating a bifurcation
WO2011119883A1 (en) 2010-03-24 2011-09-29 Advanced Bifurcation Systems, Inc. Stent alignment during treatment of a bifurcation
US9402754B2 (en) * 2010-05-18 2016-08-02 Abbott Cardiovascular Systems, Inc. Expandable endoprostheses, systems, and methods for treating a bifurcated lumen
GB201017834D0 (en) 2010-10-21 2010-12-01 Angiomed Ag System to deliver a bodily implant
US9707108B2 (en) 2010-11-24 2017-07-18 Tryton Medical, Inc. Support for treating vascular bifurcations
WO2012109382A2 (en) 2011-02-08 2012-08-16 Advanced Bifurcation Systems, Inc. Multi-stent and multi-balloon apparatus for treating bifurcations and methods of use
EP2672932B1 (en) 2011-02-08 2018-09-19 Advanced Bifurcation Systems, Inc. System for treating a bifurcation with a fully crimped stent
US8574283B1 (en) * 2011-08-30 2013-11-05 Suraj Govind Kamat Deployment of stents within bifurcated vessels
EP2841024B1 (en) 2012-04-26 2017-05-03 Tryton Medical, Inc. Support for treating vascular bifurcations
JP6246209B2 (en) * 2012-08-20 2017-12-13 アル−サードン，カーリッド Bifurcated double balloon catheter system for bifurcated body vessels
US9468545B2 (en) * 2014-04-04 2016-10-18 W. L. Gore & Associates, Inc. Bifurcated graft device
US10130465B2 (en) 2016-02-23 2018-11-20 Abbott Cardiovascular Systems Inc. Bifurcated tubular graft for treating tricuspid regurgitation
DE102016104302A1 (en) * 2016-03-09 2017-09-14 Optimed Medizinische Lnstrumente Gmbh STENT FOR USE AT BIFURCATIONS
JP2023537955A (en) * 2020-08-11 2023-09-06 シルク・ロード・メディカル・インコーポレイテッド Balloon catheter for transcarotid procedures

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE9014845U1 (en) * 1989-11-01 1991-01-10 Schneider (Europe) Ag, Zuerich, Ch
US4994071A (en) * 1989-05-22 1991-02-19 Cordis Corporation Bifurcating stent apparatus and method
FR2678508A1 (en) * 1991-07-04 1993-01-08 Celsa Lg Device for reinforcing the vessels of the human body
US5195984A (en) * 1988-10-04 1993-03-23 Expandable Grafts Partnership Expandable intraluminal graft
EP0551179A1 (en) * 1992-01-08 1993-07-14 Expandable Grafts Partnership Method and apparatus for bilateral intra-aortic bypass
EP0646365A1 (en) * 1993-10-01 1995-04-05 Juan Carlos Parodi Aortic graft, and method and apparatus for repairing an abdominal aortic aneurysm
WO1995008965A1 (en) * 1993-09-30 1995-04-06 Boston Scientific Corporation Controlled deployment of a medical device

Family Cites Families (18)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4413989A (en) * 1980-09-08 1983-11-08 Angiomedics Corporation Expandable occlusion apparatus
US4946464A (en) * 1981-07-22 1990-08-07 Pevsner Paul H Method of manufacturing miniature balloon catheter and product thereof
US4896670A (en) * 1988-04-19 1990-01-30 C. R. Bard, Inc. Kissing balloon catheter
US5143093A (en) * 1990-10-05 1992-09-01 Harvinder Sahota Methods of angioplasty treatment of stenotic regions
US5342387A (en) * 1992-06-18 1994-08-30 American Biomed, Inc. Artificial support for a blood vessel
US5723004A (en) * 1993-10-21 1998-03-03 Corvita Corporation Expandable supportive endoluminal grafts
US5609605A (en) * 1994-08-25 1997-03-11 Ethicon, Inc. Combination arterial stent
CA2134997C (en) * 1994-11-03 2009-06-02 Ian M. Penn Stent
US5613980A (en) * 1994-12-22 1997-03-25 Chauhan; Tusharsindhu C. Bifurcated catheter system and method
US5669924A (en) * 1995-10-26 1997-09-23 Shaknovich; Alexander Y-shuttle stent assembly for bifurcating vessels and method of using the same
UA58485C2 (en) * 1996-05-03 2003-08-15 Медінол Лтд. Method for manufacture of bifurcated stent (variants) and bifurcated stent (variants)
US6096073A (en) * 1997-02-25 2000-08-01 Scimed Life Systems, Inc. Method of deploying a stent at a lesion site located at a bifurcation in a parent vessel
US6165195A (en) * 1997-08-13 2000-12-26 Advanced Cardiovascylar Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US5893887A (en) * 1997-10-14 1999-04-13 Iowa-India Investments Company Limited Stent for positioning at junction of bifurcated blood vessel and method of making
WO1999024104A1 (en) * 1997-11-07 1999-05-20 Ave Connaught Balloon catheter for repairing bifurcated vessels
US6099497A (en) * 1998-03-05 2000-08-08 Scimed Life Systems, Inc. Dilatation and stent delivery system for bifurcation lesions
US6117117A (en) * 1998-08-24 2000-09-12 Advanced Cardiovascular Systems, Inc. Bifurcated catheter assembly
US6017324A (en) * 1998-10-20 2000-01-25 Tu; Lily Chen Dilatation catheter having a bifurcated balloon

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5195984A (en) * 1988-10-04 1993-03-23 Expandable Grafts Partnership Expandable intraluminal graft
US4994071A (en) * 1989-05-22 1991-02-19 Cordis Corporation Bifurcating stent apparatus and method
DE9014845U1 (en) * 1989-11-01 1991-01-10 Schneider (Europe) Ag, Zuerich, Ch
FR2678508A1 (en) * 1991-07-04 1993-01-08 Celsa Lg Device for reinforcing the vessels of the human body
EP0551179A1 (en) * 1992-01-08 1993-07-14 Expandable Grafts Partnership Method and apparatus for bilateral intra-aortic bypass
WO1995008965A1 (en) * 1993-09-30 1995-04-06 Boston Scientific Corporation Controlled deployment of a medical device
EP0646365A1 (en) * 1993-10-01 1995-04-05 Juan Carlos Parodi Aortic graft, and method and apparatus for repairing an abdominal aortic aneurysm

Cited By (129)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5961490A (en) * 1995-08-29 1999-10-05 Scimed Life Systems, Inc. Balloon perfusion catheter
US6436104B2 (en) 1996-01-26 2002-08-20 Cordis Corporation Bifurcated axially flexible stent
EP0893107A1 (en) * 1996-02-21 1999-01-27 Robert E. Fischell Expandable stent
US6540779B2 (en) 1996-05-03 2003-04-01 Medinol Ltd. Bifurcated stent with improved side branch aperture and method of making same
WO1997041803A1 (en) * 1996-05-03 1997-11-13 Divysio Solutions Ulc. Bifurcated stent and method for the manufacture of same
US6251133B1 (en) 1996-05-03 2001-06-26 Medinol Ltd. Bifurcated stent with improved side branch aperture and method of making same
US7641685B2 (en) 1996-05-03 2010-01-05 Medinol Ltd. System and method for delivering a bifurcated stent
US5827320A (en) * 1996-05-03 1998-10-27 Medinol Ltd. Bifurcated stent and method of making same
US6117156A (en) * 1996-05-03 2000-09-12 Medinol Ltd. Bifurcated stent and method of making same
US5755734A (en) * 1996-05-03 1998-05-26 Medinol Ltd. Bifurcated stent and method of making same
US7371255B2 (en) 1996-05-03 2008-05-13 Medinol Ltd. Method of making a bifurcated stent with improved side branch aperture
US6406489B1 (en) 1996-05-03 2002-06-18 Medinol, Ltd. Bifurcated stent and method of making same
US6436134B2 (en) 1996-05-03 2002-08-20 Medinol Ltd. Bifurcated stent with improved side branch aperture and method of making same
US6090133A (en) * 1996-05-03 2000-07-18 Medinol Ltd. Bifurcated stent and method of making same
AU769241B2 (en) * 1996-05-03 2004-01-22 Evysio Medical Devices Ulc Bifurcated stent and method for the manufacture of same
US6989026B2 (en) 1996-05-03 2006-01-24 Medinol Ltd. Method of making a bifurcated stent with improved side branch aperture
US5755735A (en) * 1996-05-03 1998-05-26 Medinol Ltd. Bifurcated stent and method of making same
US6955687B2 (en) 1996-05-03 2005-10-18 Medinol Ltd. Bifurcated stent with improved side branch aperture and method of making same
US6770091B2 (en) 1996-05-03 2004-08-03 Medinol Ltd. Bifurcated stent and method of making same
US6770092B2 (en) 1996-05-03 2004-08-03 Medinol Ltd. Method of delivering a bifurcated stent
US8603157B2 (en) 1996-06-06 2013-12-10 Biosensors International Group, Ltd. Endoprosthesis deployment methods for treating vascular bifurcations
US9101501B2 (en) 1996-06-06 2015-08-11 Biosensors International Group, Ltd. Bifurcation stent and method of positioning in a body lumen
US8728143B2 (en) 1996-06-06 2014-05-20 Biosensors International Group, Ltd. Endoprosthesis deployment system for treating vascular bifurcations
US9561126B2 (en) 1996-11-04 2017-02-07 Boston Scientific Scimed, Inc. Catheter with attached flexible side sheath
US6149682A (en) * 1997-01-16 2000-11-21 Medicorp R & D Benelux S.A. Luminal endoprosthesis for ramification
BE1010858A4 (en) * 1997-01-16 1999-02-02 Medicorp R & D Benelux Sa Luminal endoprosthesis FOR BRANCHING.
AU723138B2 (en) * 1997-01-16 2000-08-17 Medicorp R & D Benelux S.A. Luminal endoprosthesis for ramification
WO1998031303A1 (en) * 1997-01-16 1998-07-23 Medicorp R & D Benelux S.A. Luminal endoprosthesis for ramification
DE29701758U1 (en) * 1997-02-01 1997-03-27 Jomed Implantate Gmbh Radially expandable stent for implantation in a body vessel, particularly in the area of a vascular branch
US6096073A (en) * 1997-02-25 2000-08-01 Scimed Life Systems, Inc. Method of deploying a stent at a lesion site located at a bifurcation in a parent vessel
WO1998037833A1 (en) * 1997-02-25 1998-09-03 Symbiotech Medical, Inc. Expandable intravascular stent
US6520987B1 (en) 1997-02-25 2003-02-18 Symbiotech Medical, Inc Expandable intravascular stent
DE29708803U1 (en) * 1997-05-17 1997-07-31 Jomed Implantate Gmbh Radially expandable stent for implantation in a body vessel in the area of a vascular branch
US6682556B1 (en) 1997-07-18 2004-01-27 Vascular Concepts Holdings Limited Application catheter and method of implantation of a stent in vascular bifurcations, side branches and ostial lesions
WO1999003426A1 (en) * 1997-07-18 1999-01-28 Iowa-India Investments Company Limited An application catheter and method of implantation of a stent in vascular bifurcations, side branches and ostial lesions
EP0891751A1 (en) * 1997-07-18 1999-01-20 Thomas Prof. Dr. Ischinger Vascular stent for bifurcations, sidebranches and ostial lesions and an application catheter and method for implantation
WO1999004726A1 (en) * 1997-07-28 1999-02-04 Marco Zimarino Expandable bifurcated stent
EP2266506A1 (en) * 1997-08-13 2010-12-29 Abbott Cardiovascular Systems Inc. Stent delivery assembly for treating bifurcations
US7955379B2 (en) * 1997-08-13 2011-06-07 Abbott Cardiovascular Systems Inc. Stent and catheter assembly and method for treating bifurcations
US7708772B2 (en) 1997-08-13 2010-05-04 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
EP0897700A1 (en) * 1997-08-13 1999-02-24 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US6017363A (en) * 1997-09-22 2000-01-25 Cordis Corporation Bifurcated axially flexible stent
US7842077B2 (en) 1997-09-22 2010-11-30 Cordis Corporation Bifurcated axially flexible stent
US6746476B1 (en) 1997-09-22 2004-06-08 Cordis Corporation Bifurcated axially flexible stent
AU747698B2 (en) * 1997-09-23 2002-05-16 Design & Performance - Cyprus Limited Bifurcated stent with flexible side portion
US7018400B2 (en) * 1997-09-24 2006-03-28 Medtronic Vascular, Inc. Endolumenal prothesis and method of use in bifurcation regions of body lumens
US6315794B1 (en) 1997-11-13 2001-11-13 Medinol Ltd. Multilayered metal stent
KR100309485B1 (en) * 1997-11-13 2002-02-19 코시 리치터 Multi-layered Metal Stent
EP0916317A1 (en) * 1997-11-13 1999-05-19 Medinol Ltd. Multilayered metal stent
EP1047356B2 (en) † 1998-01-14 2014-03-12 Advanced Stent Technologies, Inc. Extendible stent apparatus
EP1905398B1 (en) 1998-01-14 2015-05-13 Advanced Stent Technologies, Inc. Extendible stent apparatus
EP1047356A1 (en) † 1998-01-14 2000-11-02 Advanced Stent Technologies, Inc. Extendible stent apparatus
EP0937442A3 (en) * 1998-02-24 2000-11-08 Cordis Corporation Bifurcated axially flexible stent
WO1999044539A3 (en) * 1998-03-05 1999-11-04 Scimed Life Systems Inc Dilatation and stent delivery system for bifurcation lesions
US7445610B2 (en) 1998-03-05 2008-11-04 Boston Scientific Scimed, Inc. Dilation and stent delivery system for bifurcation lesions
US6099497A (en) * 1998-03-05 2000-08-08 Scimed Life Systems, Inc. Dilatation and stent delivery system for bifurcation lesions
WO1999044539A2 (en) * 1998-03-05 1999-09-10 Scimed Life Systems, Inc. Dilatation and stent delivery system for bifurcation lesions
US8088102B2 (en) 1998-03-05 2012-01-03 Boston Scientific Scimed, Inc. Dilation and stent delivery system for bifurcation lesions
EP0956832A1 (en) * 1998-05-05 1999-11-17 Medinol Ltd. Bifurcated stent with improved side branch aperture and method of making same
FR2780270A1 (en) * 1998-06-25 1999-12-31 Patrice Bergeron Device for instrument positioning, used in surgical repair of damaged blood vessels
WO1999066861A1 (en) * 1998-06-25 1999-12-29 Patrice Bergeron System for three-dimensional positioning of instruments by intraluminal tract
US6143002A (en) * 1998-08-04 2000-11-07 Scimed Life Systems, Inc. System for delivering stents to bifurcation lesions
WO2000010489A1 (en) * 1998-08-24 2000-03-02 Advanced Cardiovascular Systems, Inc. Bifurcated catheter assembly
EP1466569A3 (en) * 1998-08-24 2007-08-15 Advanced Cardiovascular Systems, Inc. Bifurcated catheter assembly
JP2002523137A (en) * 1998-08-24 2002-07-30 アドバンスド、カーディオバスキュラー、システムズ、インコーポレーテッド Bifurcated catheter assembly
US6210380B1 (en) 1998-08-24 2001-04-03 Advanced Cardiovascular Systems, Inc. Bifurcated catheter assembly
US6117117A (en) * 1998-08-24 2000-09-12 Advanced Cardiovascular Systems, Inc. Bifurcated catheter assembly
US6514281B1 (en) 1998-09-04 2003-02-04 Scimed Life Systems, Inc. System for delivering bifurcation stents
US6190403B1 (en) 1998-11-13 2001-02-20 Cordis Corporation Low profile radiopaque stent with increased longitudinal flexibility and radial rigidity
US8398698B2 (en) 1999-01-27 2013-03-19 Boston Scientific Scimed, Inc. Bifurcated stent delivery system
US7476243B2 (en) 1999-01-27 2009-01-13 Boston Scientific Scimed, Inc. Bifurcation stent delivery system
EP2165676A1 (en) * 1999-06-04 2010-03-24 Advanced Stent Technologies, Inc. Catheter with side sheath
EP1857082A1 (en) * 1999-06-04 2007-11-21 Advanced Stent Technologies, Inc. Stent delivery system for branched vessel
EP1512380A1 (en) * 1999-06-04 2005-03-09 Advanced Stent Technologies, Inc. Stent delivery system for branched vessel
WO2001043665A2 (en) * 1999-12-10 2001-06-21 Advanced Cardiovascular Systems, Inc. Bifurcated stent delivery system having retractable sheath
WO2001043665A3 (en) * 1999-12-10 2002-02-21 Advanced Cardiovascular System Bifurcated stent delivery system having retractable sheath
US7540879B2 (en) 2000-02-18 2009-06-02 E.V.R. Endovascular Researches S.A. Endolumenal device for delivering and deploying an endolumenal expandable prosthesis
US8012199B2 (en) 2000-02-18 2011-09-06 Alessandro Lualdi Endolumenal device for delivering and deploying an endolumental expandable prosthesis
WO2001074273A1 (en) * 2000-03-30 2001-10-11 Advanced Cardiovascular Systems, Inc. Bifurcated stent system
AU2005203457B2 (en) * 2000-05-02 2008-06-19 Cordis Corporation Bifurcated stent and stent delivery system
EP1151730A3 (en) * 2000-05-02 2002-06-12 Cordis Corporation Bifurcated stent and stent delivery system
AU781306B2 (en) * 2000-05-02 2005-05-12 Cordis Corporation Bifurcated stent and stent delivery system
US8236048B2 (en) 2000-05-12 2012-08-07 Cordis Corporation Drug/drug delivery systems for the prevention and treatment of vascular disease
US8236041B2 (en) 2000-05-30 2012-08-07 Biosensors International Group, Ltd. Noncylindrical stent deployment system for treating vascular bifurcations
US7686845B2 (en) * 2000-05-30 2010-03-30 Devax, Inc. Noncylindrical stent deployment system for treating vascular bifurcations
US7862609B2 (en) 2000-11-16 2011-01-04 Cordis Corporation Stent graft having a pleated graft member
US6740114B2 (en) 2001-03-01 2004-05-25 Cordis Corporation Flexible stent
US6790227B2 (en) 2001-03-01 2004-09-14 Cordis Corporation Flexible stent
US8182527B2 (en) 2001-05-07 2012-05-22 Cordis Corporation Heparin barrier coating for controlled drug release
US8337540B2 (en) * 2001-05-17 2012-12-25 Advanced Cardiovascular Systems, Inc. Stent for treating bifurcations and method of use
US8231667B2 (en) 2002-11-08 2012-07-31 Jacques Séguin Endoprosthesis for vascular bifurcation
US8864817B2 (en) 2002-11-08 2014-10-21 Jacques Séguin Endoprosthesis for vascular bifurcation
US7465315B2 (en) 2003-11-19 2008-12-16 Advanced Cardiovascular Systems, Inc. Portal design for stent for treating bifurcated vessels
EP1804879A2 (en) * 2004-09-24 2007-07-11 FlowMedica, Inc. Systems and methods for bi-lateral guidewire cannulation of branched body lumens
EP1804879A4 (en) * 2004-09-24 2008-12-10 Flowmedica Inc Systems and methods for bi-lateral guidewire cannulation of branched body lumens
US9427340B2 (en) 2004-12-14 2016-08-30 Boston Scientific Scimed, Inc. Stent with protruding branch portion for bifurcated vessels
US7578831B2 (en) 2005-06-24 2009-08-25 Abbott Laboratories Balloon catheter
WO2007002423A3 (en) * 2005-06-24 2007-07-12 Abbott Lab Balloon catheter
WO2007002423A2 (en) * 2005-06-24 2007-01-04 Abbott Laboratories Balloon catheter
US8834554B2 (en) 2006-08-22 2014-09-16 Abbott Cardiovascular Systems Inc. Intravascular stent
US8882826B2 (en) 2006-08-22 2014-11-11 Abbott Cardiovascular Systems Inc. Intravascular stent
WO2008024943A1 (en) * 2006-08-23 2008-02-28 Abbott Laboratories Catheter system and method for delivering medical devices
US9492297B2 (en) 2006-09-12 2016-11-15 Boston Scientific Scimed, Inc. Multilayer balloon for bifurcated stent delivery and methods of making and using the same
US10314700B2 (en) 2007-02-05 2019-06-11 Boston Scientific Scimed, Inc. Synthetic composite structures
US10245166B2 (en) 2008-02-22 2019-04-02 Endologix, Inc. Apparatus and method of placement of a graft or graft system
US8932340B2 (en) 2008-05-29 2015-01-13 Boston Scientific Scimed, Inc. Bifurcated stent and delivery system
US10512758B2 (en) 2008-07-01 2019-12-24 Endologix, Inc. Catheter system and methods of using same
US9700701B2 (en) 2008-07-01 2017-07-11 Endologix, Inc. Catheter system and methods of using same
US10603196B2 (en) 2009-04-28 2020-03-31 Endologix, Inc. Fenestrated prosthesis
US8945202B2 (en) 2009-04-28 2015-02-03 Endologix, Inc. Fenestrated prosthesis
US9579103B2 (en) 2009-05-01 2017-02-28 Endologix, Inc. Percutaneous method and device to treat dissections
US10772717B2 (en) 2009-05-01 2020-09-15 Endologix, Inc. Percutaneous method and device to treat dissections
US9757262B2 (en) 2009-07-15 2017-09-12 Endologix, Inc. Stent graft
US10874502B2 (en) 2009-07-27 2020-12-29 Endologix Llc Stent graft
US9907642B2 (en) 2009-07-27 2018-03-06 Endologix, Inc. Stent graft
US11406518B2 (en) 2010-11-02 2022-08-09 Endologix Llc Apparatus and method of placement of a graft or graft system
US9393100B2 (en) 2010-11-17 2016-07-19 Endologix, Inc. Devices and methods to treat vascular dissections
US10660775B2 (en) 2011-03-01 2020-05-26 Endologix, Inc. Catheter system and methods of using same
US9687374B2 (en) 2011-03-01 2017-06-27 Endologix, Inc. Catheter system and methods of using same
US9549835B2 (en) 2011-03-01 2017-01-24 Endologix, Inc. Catheter system and methods of using same
EP2744457A1 (en) * 2011-08-19 2014-06-25 Al-saadon, Khalid Stent system, deployment apparatus and method for bifurcated lesion
US10463518B2 (en) 2011-08-19 2019-11-05 Khalid Al-Saadon Stent system, deployment apparatus and method for bifurcated lesion
US9486342B2 (en) 2011-08-19 2016-11-08 Khalid Al-Saadon Stent system, deployment apparatus and method for bifurcated lesion
EP2744457A4 (en) * 2011-08-19 2015-04-01 Khalid Al-Saadon Stent system, deployment apparatus and method for bifurcated lesion
US11376143B2 (en) 2011-08-19 2022-07-05 Khalid Al-Saadon Stent system deployment method for bifurcated lesion
US11129737B2 (en) 2015-06-30 2021-09-28 Endologix Llc Locking assembly for coupling guidewire to delivery system
WO2020053144A1 (en) * 2018-09-11 2020-03-19 Car Holding B.V. Kissing balloons
NL2021601B1 (en) * 2018-09-11 2020-05-01 Car Holding B V Kissing balloons and method for implementing the same
US11832827B2 (en) 2018-09-11 2023-12-05 Car Holding B.V. Kissing balloons

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CA2220141C (en) 2007-07-24
DE69629599D1 (en) 2003-09-25
US6346089B1 (en) 2002-02-12
US6183509B1 (en) 2001-02-06
ATE247436T1 (en) 2003-09-15
ES2205022T3 (en) 2004-05-01
JP3766977B2 (en) 2006-04-19
CA2220141A1 (en) 1996-11-07
EP0957818B1 (en) 2003-08-20
FR2733682B1 (en) 1997-10-31
AU709513B2 (en) 1999-09-02
DE69629599T2 (en) 2004-06-24
AU5345096A (en) 1996-11-21
JPH11504824A (en) 1999-05-11
EP0957818A1 (en) 1999-11-24
US20010039448A1 (en) 2001-11-08
FR2733682A1 (en) 1996-11-08

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