US20070213806A1 - Non-foreshortening intraluminal prosthesis - Google Patents

Non-foreshortening intraluminal prosthesis Download PDF

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Publication number
US20070213806A1
US20070213806A1 US11/726,430 US72643007A US2007213806A1 US 20070213806 A1 US20070213806 A1 US 20070213806A1 US 72643007 A US72643007 A US 72643007A US 2007213806 A1 US2007213806 A1 US 2007213806A1
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United States
Prior art keywords
stent
struts
annular element
length
annular
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Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
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US11/726,430
Inventor
Gary Roubin
Geoffrey White
Sriram Iyer
Russell Redmond
Claude Vidal
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Endosystems LLC
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Endosystems LLC
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Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=25171870&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=US20070213806(A1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Priority claimed from US10/892,718 external-priority patent/US20040267350A1/en
Application filed by Endosystems LLC filed Critical Endosystems LLC
Priority to US11/726,430 priority Critical patent/US20070213806A1/en
Publication of US20070213806A1 publication Critical patent/US20070213806A1/en
Abandoned legal-status Critical Current

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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents 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
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    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents 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
    • A61F2/915Stents 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
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    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/04Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
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    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
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    • A61F2/91Stents 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
    • A61F2/915Stents 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
    • A61F2002/91525Stents 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 within the whole structure different bands showing different meander characteristics, e.g. frequency or amplitude
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    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents 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
    • A61F2/915Stents 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
    • A61F2002/91533Stents 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
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents 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
    • A61F2/915Stents 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
    • A61F2002/91533Stents 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
    • A61F2002/91541Adjacent bands are arranged out of phase
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents 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
    • A61F2/915Stents 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
    • A61F2002/9155Adjacent bands being connected to each other
    • A61F2002/91558Adjacent bands being connected to each other connected peak to peak
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2210/00Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0014Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol
    • A61F2210/0019Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol operated at only one temperature whilst inside or touching the human body, e.g. constrained in a non-operative shape during surgery, another temperature only occurring before the operation
    • AHUMAN NECESSITIES
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    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0002Two-dimensional shapes, e.g. cross-sections
    • A61F2230/0028Shapes in the form of latin or greek characters
    • A61F2230/0054V-shaped
    • AHUMAN NECESSITIES
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    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0014Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
    • A61F2250/0029Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in bending or flexure capacity
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    • A61F2250/0039Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in diameter

Definitions

  • the present invention relates to an intraluminal prosthesis for implantation into a mammalian vessel, and in particular, to an intraluminal stent that is delivered in a compressed state to a specific location inside the lumen of a mammalian vessel and then deployed to an expanded state to support the vessel.
  • the intraluminal stent is provided with a structural configuration that maintains the prosthesis at substantially the same length in both the compressed and expanded states.
  • the intraluminal stent may also be provided with varying rigidity or flexibility along its length.
  • Intraluminal prosthesis such as stents
  • stents are commonly used in the repair of aneurysms, as liners for vessels, or to provide mechanical support to prevent the collapse of stenosed or occluded vessels.
  • These stents are typically delivered in a compressed state to a specific location inside the lumen of a vessel or other tubular structures, and then deployed at that location of the lumen to an expanded state.
  • the stent has a diameter in its expanded state which is several times larger than the diameter of the stent in its compressed state.
  • These stents are also frequently deployed in the treatment of atherosclerotic stenosis in blood vessels, especially access, it is essential that the stent's deployed diameter and length be known before the physician can accurately position a stent with the correct size at the precise location. For example, since the diameter and the length of the diseased or damaged segment or region of the body vessel can vary for different body vessels, disease states, and deployment purposes, it is important that a stent having the precise diameter and length be delivered to this region for deployment.
  • Careful sizing of this region of the lumen of the body vessel may pose a difficult challenge for many physicians who know the exact dimensions of the body vessel at this region, but are not certain about the stent's deployed diameter and length. This is due to a foreshortening effect which is experienced by many stents when they are expanded from their compressed state to their expanded state.
  • FIGS. 1A, 1B , 2 A and 2 B illustrate portions 20 of a stent having a mesh-like pattern made up of V-shaped struts or legs 22 and 24 connected at their apices 26 .
  • Two pairs of these V-shaped struts 22 , 24 are illustrated in this portion 20 of the stent.
  • Each of these struts 22 and 24 has a length h.
  • FIG. 1B illustrates the portion 20 of the stent in a fully compressed state, in which the length h has a longitudinal or horizontal component l 2 (see FIG. 2B ), and FIG.
  • FIG. 1A illustrates the same portion 20 of the stent in a fully expanded state, in which the length h has a longitudinal or horizontal component l 1 (see FIG. 2A ).
  • l 1 is shorter than l 2 because the angle which the strut 22 assumes with respect to the horizontal axis is greater when in the expanded state, so the length of the expanded portion 20 is shorter than the length of the compressed portion 20 by a length of 2 d .
  • This foreshortening is caused by the shortening of the longitudinal component l of the struts 22 and 24 as the stent is expanded from the compressed state to the expanded state.
  • This foreshortening effect is troublesome because it is not easy to determine the exact dimension of this foreshortened length 2 d .
  • the physician must make this calculation based on the material of the stent, the body vessel being treated, and the expected diameter of the stent when properly deployed in the lumen of the body vessel. For example, the foreshortened length 2 d will vary when the same stent is deployed in vessels having different diameters at the region of deployment.
  • carotid arteries An example of such a body vessel are the carotid arteries. Blood is delivered from the heart to the head via the common carotid arteries. These arteries are approximately 8-10 mm in lumen diameter as they make their way along the neck up to a position just below and behind the ear. At this point, the common carotid artery branches into a 6-8 mm lumen diameter internal carotid artery, which feeds blood to the brain, and a 6-8 mm lumen diameter external carotid artery, which supplies blood to the face and scalp. Atherosclerotic lesions of the carotid artery tend to occur around this bifurcation of the common carotid artery into the internal and external carotid arteries, so stents often need to be deployed at this bifurcation.
  • iliac arteries which have a lumen diameter of about 8-10 mm at the common iliac artery but which decrease to a lumen diameter of about 6-7 mm at the external iliac artery.
  • the common iliac arteries experience more localized stenosis or occlusive lesion which are quite often calcific and usually require a shorter stent with greater radial strength or rigidity.
  • More diffused atherosclerotic disease of the iliac system will commonly involve both the common and external iliac arteries, and necessitate a longer stent having increased flexibility that is suitable for deployment in the tortuous angulation experienced by the iliac system.
  • the femoropopliteal system similarly experiences localized and diffused stenotic lesions.
  • the flexibility of a stent is important where deployed at locations of vessels that are affected by movements of joints, such as the hip joint or the knee joint.
  • the renal arteries provide yet another useful example.
  • the initial 1 cm or so at the orifice of a renal artery is often quite firmly narrowed due to atheroma and calcification, and is relatively straight, while the remainder of the length of the renal artery is relatively curved.
  • a stent intended for implantation at the renal arteries should be relatively rigid for its first 1.5 cm or so, and then become more flexible and compliant.
  • an intraluminal prosthesis that maintains a consistent length in both its fully compressed and fully expanded states, and in all states between its fully compressed and fully expanded states.
  • a stent which can accommodate body vessels having varying lumen diameters, different anatomies, and different disease states.
  • a stent having a plurality of annular elements.
  • Each annular element has a compressed state and an expanded state, and has a longitudinal dimension which is smaller in the expanded state than in the compressed state.
  • a plurality of connecting members connect adjacent annular elements, with the connecting members operating to compensate for the smaller longitudinal dimension of each annular element in the expanded state.
  • each annular element includes a plurality of struts and apices connected to form an annular configuration.
  • the connecting members are connected to the apices of the adjacent annular elements.
  • the plurality of struts of the annular elements include left and right struts, with each pair of left and right struts connected to each other at an apex.
  • Each strut has a longitudinal dimension which is smaller when the annular element is in the expanded state than in the compressed state.
  • At least one of the annular elements may have a closed configuration such that the plurality of alternating struts and apices are connected to each other to form a closed annular element.
  • at least one of the annular elements may assume an open configuration such that the plurality of alternating struts and apices are not connected at at least one location.
  • the connecting members have a plurality of alternating segments.
  • the connecting members have a plurality of alternating curved segments defining alternating top and bottom curved apices.
  • the connecting members have a plurality of alternating curved and straight segments.
  • the connecting members have a plurality of alternating and angled straight segments. The connecting members have a larger longitudinal dimension when each annular element is in the expanded state than in the compressed state to compensate for the smaller longitudinal dimension of the annular element in the expanded state.
  • the stent according to the present invention further includes a plurality of apertures defined by adjacent annular elements and connecting members. In one embodiment, it is possible for the apertures of different segments of the stent to have different sizes.
  • the stent according to the present invention further provides a plurality of segments, at least two of which have a different degree of flexibility.
  • the varying flexibility is accomplished by forming a plurality of gaps. These gaps may be formed by omitting one or more of the connecting members, or portions of connecting members, between adjacent annular elements, or by omitting one or more of the struts, or by omitting connecting members and struts.
  • the varying flexibility is accomplished by providing the apertures of different stent segments with different sizes.
  • the stent according to the present invention may further provide segments that assume different diameters when the stent is in its expanded state.
  • the differing diameters may be accomplished by providing the stent in a tapered or a stepped configuration.
  • the stent is made from a shape memory alloy, such as Nitinol, although other materials such as stainless steel, tantalum, titanium, elgiloy, gold, platinum, or any other metal or alloy, or polymers or composites, having sufficient biocompatibility, rigidity, flexibility, radial strength, radiopacity and antithrombogenicity can be used for the stent material.
  • a shape memory alloy such as Nitinol
  • other materials such as stainless steel, tantalum, titanium, elgiloy, gold, platinum, or any other metal or alloy, or polymers or composites, having sufficient biocompatibility, rigidity, flexibility, radial strength, radiopacity and antithrombogenicity can be used for the stent material.
  • the stent according to the present invention maintains a consistent length in both its fully compressed and fully expanded states, and in all states between its fully compressed and fully expanded states.
  • the stent according to the present invention facilitates accurate sizing and deployment, thereby simplifying, and possibly reducing the time needed for, the medical procedure.
  • the stent according to the present invention provides varying flexibility and rigidity along its length and/or circumference, as well as varying diameters along different segments of the stent, thereby facilitating the treatment of body vessels having varying lumen diameters, different anatomies and different disease states.
  • FIG. 1A is a side elevational view of a portion of a prior art stent in its expanded state
  • FIG. 1B is a side elevational view of the portion of FIG. 1A in its compressed state
  • FIG. 2A illustrates the longitudinal component of a strut of the stent of FIGS. 1A and 1B when the stent is in its expanded state
  • FIG. 2B illustrates the longitudinal component of a strut of the stent of FIGS. 1A and 1B when the stent is in its compressed state
  • FIG. 3 is a perspective view of a stent according to the present invention.
  • FIG. 4A is a side elevational view of a portion of the stent of FIG. 3 in its expanded state
  • FIG. 4B is a side elevational view of the portion of FIG. 4A in its compressed state
  • FIG. 5A illustrates the longitudinal component of a strut and its connecting member of the stent of FIGS. 4A and 4B when the stent is in its expanded state
  • FIG. 5B illustrates the longitudinal component of a strut and its connecting member of the stent of FIGS. 4A and 4B when the stent is in its compressed state
  • FIG. 6A is a side elevational view of the stent of FIG. 3 in its expanded state
  • FIG. 6B is a side elevational view of the stent of FIG. 6A in its compressed state
  • FIGS. 7 and 8 illustrate alternative embodiments of the connecting member according to the present invention
  • FIG. 9 is a side elevational view of a portion of the stent of FIG. 3 illustrating a modification thereto;
  • FIG. 10 is a side elevational view of a portion of the stent of FIG. 3 illustrating another modification thereto;
  • FIGS. 11A-11C illustrate modifications to the stent of FIG. 3 .
  • the intraluminal prosthesis according to the present invention is a stent, although the principles of the present invention are also applicable to other prosthesis such as liners and filters.
  • the stent is delivered to a desired location in the lumen of a body vessel in a compressed state, and is then deployed by expanding it to its expanded state.
  • the stent maintains substantially the same length in both its fully compressed and fully expanded states, and in all states between these two states.
  • the stent may be provided with varying flexibility or rigidity along different segments thereof to allow the stent to be deployed in body vessels having different anatomies and different disease states.
  • the stent may also be provided in a configuration in which the same stent has varying diameters along different portions of the stent to facilitate implantation in body vessels that have varying diameters.
  • the stent according to the present invention can be a self-expanding stent, or a stent that is radially expandable by inflating a balloon or expanded by an expansion member, or a stent that is expanded by the use of radio frequency which provides heat to cause the stent to change its size.
  • the stent may also be coated with coverings of PTFE, dacron, or other biocompatible materials to form a combined stent-graft prosthesis.
  • the vessels in which the stent of the present invention can be deployed include but are not limited to natural body vessels such as ducts, arteries, trachea, veins, ureters and the esophagus, and artificial vessels such as grafts.
  • FIGS. 3-6 A stent 40 according to the present invention is illustrated in FIGS. 3-6 in its expanded state.
  • the stent 40 has a tubular configuration and is made up of a plurality of pairs of substantially V-shaped struts connected at their apices, and by connecting a plurality of connecting members to the apices of each pair of V-shaped struts.
  • FIGS. 4A and 4B illustrate a portion of the stent 40 in greater detail.
  • the stent 40 has a plurality of pairs of alternating left struts 42 and right struts 44 . Each pair of left and right struts 42 , 44 is connected at an apex 46 to form a substantially V-shape for the pair.
  • the left strut 42 is defined as being to the left of each apex 46
  • the right strut 44 is defined as being to the right of each apex 46
  • the left struts 42 and right struts 44 are alternating since the left strut 42 of one pair of V-shaped struts is also the left strut of the adjacent pair of V-shaped struts, and the right strut 44 of one pair of V-shaped struts is also the right strut of the adjacent pair of V-shaped struts. In this manner, the alternating left and right struts 42 and 44 extend in an annular manner around the tubular stent 40 to form an annular element.
  • each apex 46 is connected to another apex 46 by a connecting member 48 . Therefore, the stent 40 resembles a tubular lattice formed by pairs of V-shaped struts 42 , 44 connected to themselves and having their apices 46 connected by the connecting members 48 . As shown in FIG. 3 , both ends of the stent 40 are defined by a plurality of alternating left and right struts 42 , 44 , with the extremity of both ends defined by the apices 46 of these alternating left and right struts 42 , 44 .
  • the connecting members 48 have a configuration that includes a plurality or pattern of alternating segments.
  • a non-limiting first preferred embodiment of the connecting member 48 is illustrated in FIGS. 4A and 4B .
  • Each connecting member 48 extends longitudinally along a longitudinal extension 52 from an apex 46 , then slopes upwardly along a curved segment 54 to a top curved apex 56 , at which point the connecting member 48 slopes downwardly along a curved segment 58 to a bottom curved apex 60 .
  • the connecting member 48 then slopes upwardly along a curved segment 62 to another top curved apex 64 .
  • the connecting member 48 slopes downwardly along a curved segment 66 to a longitudinal extension 68 of the opposing apex 46 .
  • the connecting member 48 has a plurality of alternating curved segments that are defined by the alternating top and bottom apices 56 , 60 and 64 .
  • the connecting members 48 are provided to perform two functions. First, the connecting members 48 connect pairs of apices 46 . Second, the connecting members 48 function to compensate for the foreshortening experienced by the longitudinal component of each strut 42 and 44 , thereby maintaining the stent 40 at substantially the same length at all times. This is accomplished by providing the connecting member 48 with a natural bias and a springy nature, which together with its alternating segments, combine to shorten its length when compressed. When allowed to expand, the connecting member 48 is biased to return to its natural or original position, which lengthens the connecting member 48 to compensate for the foreshortening experienced by the longitudinal component of each strut 42 and 44 .
  • FIGS. 4A, 4B , 5 A and 5 B This effect is illustrated in FIGS. 4A, 4B , 5 A and 5 B.
  • the connecting member 48 When the stent 40 is in its compressed state, the connecting member 48 has a length of L 2 , which is less than the length L 1 when the connecting member 48 is in its expanded state.
  • the connecting member 48 When the connecting member 48 is in the compressed state, its alternating curves have a higher amplitude and a smaller wavelength than when it is in the expanded state (compare FIGS. 4A and 4B ).
  • the difference between L 2 and L 1 compensates for the difference between l 1 and l 2 of the struts 42 , 44 at both ends of the connecting member 48 .
  • FIGS. 6A and 6B also show that the relevant portion of the stent 40 does not experience any foreshortening, and the lines 74 and 76 in FIGS. 6A and 6B show that the entire stent 40 maintains a consistent length through all its states.
  • connecting members 48 have been described in FIGS. 4A, 4B , 5 A and 5 B as assuming a particular configuration, it will be appreciated by those skilled in the art that the connecting members 48 can assume other configurations without departing from the spirit and scope of the present invention.
  • the connecting members 48 can be provided in any curved, partially curved, or other configuration as long as they function to compensate for the foreshortening experienced by the longitudinal component of each strut 42 and 44 .
  • FIG. 7 illustrates a non-limiting second preferred embodiment of the connecting member, in which the connecting member 48 a has alternating curved segments 80 and straight segments 82 .
  • the connecting member 48 a When the connecting member 48 a is compressed, its curved segments 80 also have a higher amplitude and a smaller wavelength than when it is in its expanded state.
  • FIG. 8 illustrates a non-limiting second preferred embodiment, in which the connecting member 48 b has alternating straight segments 84 and 86 that are angled with respect to each other.
  • the stent 40 When the stent 40 is in its fully expanded state, it preferably has an outer diameter that is slightly larger than the inner diameter of the region of the body vessel at which it is to be deployed. This allows the stent 40 to be securely anchored at the desired location and prevents the stent 40 from migrating away from the deployed location.
  • the stent 40 can be provided with varying flexibility or rigidity at different portions or segments along its length to facilitate deployment in body vessels that require such varying flexibility or rigidity.
  • the varying flexibility or rigidity can be accomplished by omitting connecting members 48 and struts 42 , 44 , or by not connecting one or more struts 32 , 44 and/or connecting members 48 , thereby creating “gaps” at one or more locations along the stent 40 . These locations can be anywhere along the length and/or the circumference of the stent 40 .
  • varying degrees of flexibility in the stent 40 can be accomplished by varying the patterns of these gaps.
  • a non-limiting example would be to provide a substantially spiral pattern of omitted struts 42 , 44 and/or connecting members 48 , such as illustrated in FIG. 9 .
  • the omitted struts 42 , 44 and connecting members 48 are illustrated in FIG. 9 in phantom (i.e., the dotted lines) by the numerals 47 (for the struts 42 , 44 ) and 49 (for the connecting members).
  • the omitted struts 47 assume a relatively spiral pattern along the length of the stent 40 from the top left corner of FIG. 9 to the bottom right corner of FIG. 9 , and can extend around the circumference of the stent 40 .
  • the omitted connecting members 49 assume a relatively spiral pattern along the length of the stent 40 from the bottom left corner of FIG. 9 to the top right corner of FIG. 9 , and can extend around the circumference of the stent 40 .
  • non-limiting alternatives include providing such gaps 49 at one or both ends of the stent 40 only, or at a central portion of the stent 40 . Further non-limiting alternatives would be to increase the number of these gaps 47 , 49 from one or both ends of the stent 40 towards the center of the stent 40 , or to increase the number of these gaps 47 , 49 from the center of the stent 40 towards one or both ends of the stent 40 . It is also possible to omit only a portion of certain connecting members 48 and not the entire ones of these connecting members 48 . A portion of the stent 40 having a larger number of gaps 47 , 49 would have greater flexibility or reduced rigidity.
  • annular elements that are made up of the alternating struts 42 , 44 may be closed or constitute completely connected annular elements, while some of these annular elements will be open annular elements.
  • the varying flexibility or rigidity can also be accomplished by providing a structural configuration where the size of the open areas or apertures 78 (for example, see FIGS. 4A and 10 ) defined between the struts 42 , 44 and the connecting members 48 is varied at different portions or segments of the stent 40 , along the length and/or circumference of the stent 40 .
  • all the apertures 78 in one segment of the stent 40 have substantially the same first size
  • all the apertures 78 in another segment of the stent 40 have substantially the same second size, the first and second sizes being different. Additional segments, each having apertures 78 with substantially the same size as the other apertures 78 in that segment but having a different size as the apertures 78 in other segments, can also be provided.
  • Varying the size of apertures 78 can be accomplished by varying the lengths of the struts 42 , 44 and the connecting members 48 .
  • a smaller aperture 78 can be provided by shortening the lengths of the struts 42 , 44 and the connecting members 48 that define the particular open area 78 .
  • Portions of the stent 40 with smaller apertures 78 are more rigid and less flexible than portions of the stent 40 with larger apertures 78 . This allows the stent 40 to be deployed in body vessels that require a stent to be more rigid at one end, and to be increasingly flexible from the rigid end. Examples of such body vessels include the renal and iliac arteries discussed above.
  • Varying the sizes of the apertures 78 also serves other important purposes. For example, providing smaller apertures 78 at the opposing ends of the stent 40 provides increased or closer coverage of the vessel wall, thereby improving support of the diseased vessel wall and preventing fragments of the plaque from being dislodged as embolic debris. The dislodgement of debris can be dangerous in certain vessels, such as the carotid arteries, where dislodged debris can be carried to the brain, possibly resulting in a stroke. As another example, providing larger apertures 78 at central portions of the stent 40 provides wider open areas that may be important in preventing the obstruction of side branches of other body vessels. These wider open areas also allow the passage of guidewires, catheters, stents, grafts, and other deployment devices through the body of the stent 40 into these side branches.
  • the stent 40 can also be provided in a manner in which it assumes a constant diameter in its compressed state, but in which different portions of the stent 40 can assume different diameters when in their fully expanded states. Providing an expandable stent 40 with the capability of assuming different diameters at different portions is important where the stent 40 is used in certain body vessels or branches of body vessels where the lumen diameters may vary. Examples of such body vessels and branches include the carotid and iliac arteries discussed above, and the esophagus.
  • the varying stent diameter can be provided in a number of ways.
  • a first non-limiting alternative is to provide a gradually tapered configuration of the stent 40 a , as shown in FIG. 11A .
  • a tapered configuration is best-suited for use in body vessels which experience a gradual narrowing.
  • a second non-limiting alternative is to provide an abrupt transition, such as a stepped configuration, between two stent segments 30 each having a relatively consistent, but different, diameter.
  • the step can be for a step-up 40 c , as shown in FIG. 1C , or for a step-down 40 b , as shown in FIG. 11B .
  • a stent 40 can be provided with several changes in diameter along its length to match specific anatomical requirements.
  • the tapering or transitioning of the stent configuration can be accomplished by pre-shaping, and can be enhanced by variations in (1) the thickness of the stent material, (2) the size of apertures 78 , and (3) the gaps 47 , 49 .
  • varying flexibility and rigidity can also be accomplished by varying the width or thickness of the stent material at certain locations along the length and/or circumference of the stent 40 .
  • the stent 40 (including its struts 42 , 44 and connecting members 48 ) is preferably made of a shape memory superelastic metal alloy such as Nitinol, which has the unusual property of “mechanical” memory and trainability.
  • This alloy can be formed into a first predetermined shape above a transition temperature range. The alloy may be plastically deformed into a second shape below the transition temperature range, but the alloy will completely recover to its original (first predetermined) shape when raised back above the transition temperature range.
  • the Nitinol preferably has a composition of about 50% nickel and about 50% titanium.
  • shape memory alloys such as Nitinol and their use in stents have been well-documented in the literature, and reference can be made to the article by T. W. Duerig, A. R. Pelton and D. Stockel entitled “The Use of Superelasticity in Medicine”, a copy of which is attached hereto and specifically incorporated into this specification by specific reference thereto as though fully set forth herein.
  • the stent 40 (including its struts 42 , 44 and connecting members 48 ) can be made of stainless steel, tantalum, titanium, elgiloy, gold, platinum, or any other metal or alloy, or polymers or composites, having sufficient biocompatibility, rigidity, flexibility, radial strength, radiopacity and antithrombogenicity.
  • connecting members 48 have been described above as having the same material as the struts 42 , 44 , it is possible to provide the connecting members 48 with a different material without departing from the spirit and scope of the present invention.
  • a material should be springy in nature and should allow the connecting members 48 to be compressed and expanded in the longitudinal direction to compensate for the foreshortening experienced by the struts 42 and 44 .
  • Non-limiting examples of such materials can include any of the materials described above for the stent 40 .
  • the stent 40 can be made from one of a number of methods, depending on the material of the stent 40 and the desired nature of deployment.
  • the stent 40 is fabricated from a solid Nitinol tube with dimensions that are identical to the stent 40 when it is in the fully compressed state.
  • the pattern of the stent 40 i.e., its struts 42 , 44 and connecting members 48 ) is programmed into a computer-guided laser cutter or lathe which cuts out the segments between the struts 42 , 44 and the connecting members 48 in a manner which closely controls the outside diameter and wall thickness of the stent 40 .
  • the stent 40 is progressively expanded until it reaches its fully expanded state.
  • the expansion can be performed by an internal expansion fixture, although other expansion apparatus and methods can be used without departing from the spirit and scope of the present invention.
  • the overall length of the stent 40 must be consistently maintained throughout the expansion of the stent 40 from its fully compressed to its fully expanded states.
  • the stent 40 Once the stent 40 has been expanded to its fully expanded state, it is heat-treated to “set” the shape memory of the Nitinol material to the fully expanded dimensions. The stent 40 is then cleaned and electro-polished.
  • the next step is to compress the stent 40 again into a dimension which allows for delivery into a vessel, either through percutaneous delivery or through minimally invasive surgical procedures.
  • the stent 40 must be compressed into a smaller state so that it can be delivered by a delivery device to the desired location of the vessel. Any conventional delivery device could be used, such as but not limited to a tube, catheter, or sheath.
  • This compression is accomplished by cooling the stent 40 to a low temperature, for example, zero degrees Celcius, and while maintaining this temperature, compressing the stent 40 to allow the stent 40 to be inserted inside the delivery device. Once inserted inside the delivery device, the stent 40 is held by the delivery device in the compressed state at room temperature.
  • a balloon-expandable stent 40 can be fabricated by connecting a plurality of wires that have been bent or formed into the desired shapes for the struts 42 , 44 and connecting members 48 .
  • the connection can be accomplished by welding, tying, bonding, or any other conventional method.
  • wire electro-discharge machining can be used.
  • the wires are capable of experiencing plastic deformation when the stent 40 is compressed, and when the stent 40 is expanded. Upon plastic deformation of the stent 40 to either the compressed or the expanded state, the stent 40 remains in this state until another force is applied to plastically deform the stent 40 again.
  • the stent 40 can be deployed by a number of delivery systems and delivery methods. These delivery systems and methods will vary depending on whether the stent 40 is expanded by self-expansion, radial expansion forces, or radio frequency.

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Abstract

An intraluminal prosthesis is provided with a plurality of annular elements. Each annular element includes a plurality of struts and apices connected to form an annular configuration. Each annular element has a compressed state and an expanded state, and has a longitudinal dimension which is smaller in the expanded state than in the compressed state. A plurality of connecting members connect the apices of adjacent annular elements. The connecting members have a plurality of alternating segments that function to compensate for the smaller longitudinal dimension of each annular element in the expanded state. The stent may be provided with varying flexibility along its length and/or circumference, and may include segments that have different diameters.

Description

    RELATED CASES
  • This is a continuation application of co-pending Ser. No. 10/892,718, entitled “Non-Foreshortening Intraluminal Prosthesis”, filed Jul. 16, 2004, which is a continuation of Ser. No. 10/283,957, entitled “Non-Foreshortening Intraluminal Prosthesis”, filed Oct. 30, 2002, now U.S. Pat. No. 6,764,506, which is a continuation of Ser. No. 09/641,121, entitled “Non-Foreshortening Intraluminal Prosthesis”, filed Aug. 17, 2000, now U.S. Pat. No. 6,475,236, which is a continuation application of co-pending Ser. No. 09/179,021, entitled “Non-Foreshortening Intraluminal Prosthesis”, filed Oct. 26, 1998, now U.S. Pat. No. 6,106,548, which is a divisional of Ser. No. 08/797,814, entitled “Non-Foreshortening Intraluminal Prosthesis”, filed Feb. 7, 1997, U.S. Pat. No. 5,827,321, whose disclosures are incorporated by this reference as though fully set forth herein.
  • BACKGROUND OF THE INVENTION
  • 1. Field of the Invention
  • The present invention relates to an intraluminal prosthesis for implantation into a mammalian vessel, and in particular, to an intraluminal stent that is delivered in a compressed state to a specific location inside the lumen of a mammalian vessel and then deployed to an expanded state to support the vessel. The intraluminal stent is provided with a structural configuration that maintains the prosthesis at substantially the same length in both the compressed and expanded states. The intraluminal stent may also be provided with varying rigidity or flexibility along its length.
  • 2. Description of the Prior Art
  • Intraluminal prosthesis, such as stents, are commonly used in the repair of aneurysms, as liners for vessels, or to provide mechanical support to prevent the collapse of stenosed or occluded vessels. These stents are typically delivered in a compressed state to a specific location inside the lumen of a vessel or other tubular structures, and then deployed at that location of the lumen to an expanded state.
  • The stent has a diameter in its expanded state which is several times larger than the diameter of the stent in its compressed state. These stents are also frequently deployed in the treatment of atherosclerotic stenosis in blood vessels, especially access, it is essential that the stent's deployed diameter and length be known before the physician can accurately position a stent with the correct size at the precise location. For example, since the diameter and the length of the diseased or damaged segment or region of the body vessel can vary for different body vessels, disease states, and deployment purposes, it is important that a stent having the precise diameter and length be delivered to this region for deployment.
  • Careful sizing of this region of the lumen of the body vessel may pose a difficult challenge for many physicians who know the exact dimensions of the body vessel at this region, but are not certain about the stent's deployed diameter and length. This is due to a foreshortening effect which is experienced by many stents when they are expanded from their compressed state to their expanded state.
  • This foreshortening effect is illustrated in FIGS. 1A, 1B, 2A and 2B, which illustrate portions 20 of a stent having a mesh-like pattern made up of V-shaped struts or legs 22 and 24 connected at their apices 26. Two pairs of these V- shaped struts 22, 24 are illustrated in this portion 20 of the stent. Each of these struts 22 and 24 has a length h. FIG. 1B illustrates the portion 20 of the stent in a fully compressed state, in which the length h has a longitudinal or horizontal component l2 (see FIG. 2B), and FIG. 1A illustrates the same portion 20 of the stent in a fully expanded state, in which the length h has a longitudinal or horizontal component l1 (see FIG. 2A). As illustrated by the imaginary lines 28 and 30 in FIGS. 1A and 1B, and in FIGS. 2A and 2B, l1 is shorter than l2 because the angle which the strut 22 assumes with respect to the horizontal axis is greater when in the expanded state, so the length of the expanded portion 20 is shorter than the length of the compressed portion 20 by a length of 2 d. This foreshortening is caused by the shortening of the longitudinal component l of the struts 22 and 24 as the stent is expanded from the compressed state to the expanded state.
  • This foreshortening effect is troublesome because it is not easy to determine the exact dimension of this foreshortened length 2 d. The physician must make this calculation based on the material of the stent, the body vessel being treated, and the expected diameter of the stent when properly deployed in the lumen of the body vessel. For example, the foreshortened length 2 d will vary when the same stent is deployed in vessels having different diameters at the region of deployment.
  • In addition, there are certain body vessels that experience a change in vessel lumen diameter, anatomy or disease state along their lengths. Stents to be deployed at such vessels will need to be capable of addressing or adapting to these changes.
  • An example of such a body vessel are the carotid arteries. Blood is delivered from the heart to the head via the common carotid arteries. These arteries are approximately 8-10 mm in lumen diameter as they make their way along the neck up to a position just below and behind the ear. At this point, the common carotid artery branches into a 6-8 mm lumen diameter internal carotid artery, which feeds blood to the brain, and a 6-8 mm lumen diameter external carotid artery, which supplies blood to the face and scalp. Atherosclerotic lesions of the carotid artery tend to occur around this bifurcation of the common carotid artery into the internal and external carotid arteries, so stents often need to be deployed at this bifurcation.
  • Another example are the iliac arteries, which have a lumen diameter of about 8-10 mm at the common iliac artery but which decrease to a lumen diameter of about 6-7 mm at the external iliac artery. The common iliac arteries experience more localized stenosis or occlusive lesion which are quite often calcific and usually require a shorter stent with greater radial strength or rigidity. More diffused atherosclerotic disease of the iliac system will commonly involve both the common and external iliac arteries, and necessitate a longer stent having increased flexibility that is suitable for deployment in the tortuous angulation experienced by the iliac system.
  • The femoropopliteal system similarly experiences localized and diffused stenotic lesions. In addition, the flexibility of a stent is important where deployed at locations of vessels that are affected by movements of joints, such as the hip joint or the knee joint.
  • The renal arteries provide yet another useful example. The initial 1 cm or so at the orifice of a renal artery is often quite firmly narrowed due to atheroma and calcification, and is relatively straight, while the remainder of the length of the renal artery is relatively curved. As a result, a stent intended for implantation at the renal arteries should be relatively rigid for its first 1.5 cm or so, and then become more flexible and compliant.
  • Thus, there remains a need for an intraluminal prosthesis that maintains a consistent length in both its fully compressed and fully expanded states, and in all states between its fully compressed and fully expanded states. There also remains a need for a stent which can accommodate body vessels having varying lumen diameters, different anatomies, and different disease states.
  • SUMMARY OF THE DISCLOSURE
  • In order to accomplish the objects of the present invention, there is provided a stent having a plurality of annular elements. Each annular element has a compressed state and an expanded state, and has a longitudinal dimension which is smaller in the expanded state than in the compressed state. A plurality of connecting members connect adjacent annular elements, with the connecting members operating to compensate for the smaller longitudinal dimension of each annular element in the expanded state.
  • In one embodiment of the present invention, each annular element includes a plurality of struts and apices connected to form an annular configuration. The connecting members are connected to the apices of the adjacent annular elements. The plurality of struts of the annular elements include left and right struts, with each pair of left and right struts connected to each other at an apex. Each strut has a longitudinal dimension which is smaller when the annular element is in the expanded state than in the compressed state.
  • In one embodiment of the present invention, at least one of the annular elements may have a closed configuration such that the plurality of alternating struts and apices are connected to each other to form a closed annular element. In addition, it is also possible for at least one of the annular elements to assume an open configuration such that the plurality of alternating struts and apices are not connected at at least one location.
  • In a preferred embodiment of the present invention, the connecting members have a plurality of alternating segments. In one embodiment, the connecting members have a plurality of alternating curved segments defining alternating top and bottom curved apices. In another embodiment, the connecting members have a plurality of alternating curved and straight segments. In a further embodiment, the connecting members have a plurality of alternating and angled straight segments. The connecting members have a larger longitudinal dimension when each annular element is in the expanded state than in the compressed state to compensate for the smaller longitudinal dimension of the annular element in the expanded state.
  • The stent according to the present invention further includes a plurality of apertures defined by adjacent annular elements and connecting members. In one embodiment, it is possible for the apertures of different segments of the stent to have different sizes.
  • The stent according to the present invention further provides a plurality of segments, at least two of which have a different degree of flexibility. In one embodiment, the varying flexibility is accomplished by forming a plurality of gaps. These gaps may be formed by omitting one or more of the connecting members, or portions of connecting members, between adjacent annular elements, or by omitting one or more of the struts, or by omitting connecting members and struts. In another embodiment, the varying flexibility is accomplished by providing the apertures of different stent segments with different sizes.
  • The stent according to the present invention may further provide segments that assume different diameters when the stent is in its expanded state. The differing diameters may be accomplished by providing the stent in a tapered or a stepped configuration.
  • In a preferred embodiment according to the present invention, the stent is made from a shape memory alloy, such as Nitinol, although other materials such as stainless steel, tantalum, titanium, elgiloy, gold, platinum, or any other metal or alloy, or polymers or composites, having sufficient biocompatibility, rigidity, flexibility, radial strength, radiopacity and antithrombogenicity can be used for the stent material.
  • Thus, the stent according to the present invention maintains a consistent length in both its fully compressed and fully expanded states, and in all states between its fully compressed and fully expanded states. As a result, the stent according to the present invention facilitates accurate sizing and deployment, thereby simplifying, and possibly reducing the time needed for, the medical procedure. In addition, the stent according to the present invention provides varying flexibility and rigidity along its length and/or circumference, as well as varying diameters along different segments of the stent, thereby facilitating the treatment of body vessels having varying lumen diameters, different anatomies and different disease states.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1A is a side elevational view of a portion of a prior art stent in its expanded state;
  • FIG. 1B is a side elevational view of the portion of FIG. 1A in its compressed state;
  • FIG. 2A illustrates the longitudinal component of a strut of the stent of FIGS. 1A and 1B when the stent is in its expanded state;
  • FIG. 2B illustrates the longitudinal component of a strut of the stent of FIGS. 1A and 1B when the stent is in its compressed state;
  • FIG. 3 is a perspective view of a stent according to the present invention;
  • FIG. 4A is a side elevational view of a portion of the stent of FIG. 3 in its expanded state;
  • FIG. 4B is a side elevational view of the portion of FIG. 4A in its compressed state;
  • FIG. 5A illustrates the longitudinal component of a strut and its connecting member of the stent of FIGS. 4A and 4B when the stent is in its expanded state;
  • FIG. 5B illustrates the longitudinal component of a strut and its connecting member of the stent of FIGS. 4A and 4B when the stent is in its compressed state;
  • FIG. 6A is a side elevational view of the stent of FIG. 3 in its expanded state;
  • FIG. 6B is a side elevational view of the stent of FIG. 6A in its compressed state;
  • FIGS. 7 and 8 illustrate alternative embodiments of the connecting member according to the present invention;
  • FIG. 9 is a side elevational view of a portion of the stent of FIG. 3 illustrating a modification thereto;
  • FIG. 10 is a side elevational view of a portion of the stent of FIG. 3 illustrating another modification thereto; and
  • FIGS. 11A-11C illustrate modifications to the stent of FIG. 3.
  • DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
  • The following detailed description is of the best presently contemplated modes of carrying out the invention. This description is not to be taken in a limiting sense, but is made merely for the purpose of illustrating general principles of embodiments of the invention. The scope of the invention is best defined by the appended claims.
  • The intraluminal prosthesis according to the present invention is a stent, although the principles of the present invention are also applicable to other prosthesis such as liners and filters. The stent is delivered to a desired location in the lumen of a body vessel in a compressed state, and is then deployed by expanding it to its expanded state. The stent maintains substantially the same length in both its fully compressed and fully expanded states, and in all states between these two states. The stent may be provided with varying flexibility or rigidity along different segments thereof to allow the stent to be deployed in body vessels having different anatomies and different disease states. The stent may also be provided in a configuration in which the same stent has varying diameters along different portions of the stent to facilitate implantation in body vessels that have varying diameters.
  • The stent according to the present invention can be a self-expanding stent, or a stent that is radially expandable by inflating a balloon or expanded by an expansion member, or a stent that is expanded by the use of radio frequency which provides heat to cause the stent to change its size. The stent may also be coated with coverings of PTFE, dacron, or other biocompatible materials to form a combined stent-graft prosthesis. The vessels in which the stent of the present invention can be deployed include but are not limited to natural body vessels such as ducts, arteries, trachea, veins, ureters and the esophagus, and artificial vessels such as grafts.
  • 1. A Preferred Embodiment
  • A stent 40 according to the present invention is illustrated in FIGS. 3-6 in its expanded state. Referring to FIG. 3, the stent 40 has a tubular configuration and is made up of a plurality of pairs of substantially V-shaped struts connected at their apices, and by connecting a plurality of connecting members to the apices of each pair of V-shaped struts. FIGS. 4A and 4B illustrate a portion of the stent 40 in greater detail. The stent 40 has a plurality of pairs of alternating left struts 42 and right struts 44. Each pair of left and right struts 42, 44 is connected at an apex 46 to form a substantially V-shape for the pair. The left strut 42 is defined as being to the left of each apex 46, and the right strut 44 is defined as being to the right of each apex 46. The left struts 42 and right struts 44 are alternating since the left strut 42 of one pair of V-shaped struts is also the left strut of the adjacent pair of V-shaped struts, and the right strut 44 of one pair of V-shaped struts is also the right strut of the adjacent pair of V-shaped struts. In this manner, the alternating left and right struts 42 and 44 extend in an annular manner around the tubular stent 40 to form an annular element. Each apex 46 is connected to another apex 46 by a connecting member 48. Therefore, the stent 40 resembles a tubular lattice formed by pairs of V-shaped struts 42, 44 connected to themselves and having their apices 46 connected by the connecting members 48. As shown in FIG. 3, both ends of the stent 40 are defined by a plurality of alternating left and right struts 42, 44, with the extremity of both ends defined by the apices 46 of these alternating left and right struts 42, 44.
  • The connecting members 48 have a configuration that includes a plurality or pattern of alternating segments. A non-limiting first preferred embodiment of the connecting member 48 is illustrated in FIGS. 4A and 4B. Each connecting member 48 extends longitudinally along a longitudinal extension 52 from an apex 46, then slopes upwardly along a curved segment 54 to a top curved apex 56, at which point the connecting member 48 slopes downwardly along a curved segment 58 to a bottom curved apex 60. The connecting member 48 then slopes upwardly along a curved segment 62 to another top curved apex 64. From the top curved apex 64, the connecting member 48 slopes downwardly along a curved segment 66 to a longitudinal extension 68 of the opposing apex 46. Thus, the connecting member 48 has a plurality of alternating curved segments that are defined by the alternating top and bottom apices 56, 60 and 64.
  • The connecting members 48 are provided to perform two functions. First, the connecting members 48 connect pairs of apices 46. Second, the connecting members 48 function to compensate for the foreshortening experienced by the longitudinal component of each strut 42 and 44, thereby maintaining the stent 40 at substantially the same length at all times. This is accomplished by providing the connecting member 48 with a natural bias and a springy nature, which together with its alternating segments, combine to shorten its length when compressed. When allowed to expand, the connecting member 48 is biased to return to its natural or original position, which lengthens the connecting member 48 to compensate for the foreshortening experienced by the longitudinal component of each strut 42 and 44.
  • This effect is illustrated in FIGS. 4A, 4B, 5A and 5B. When the stent 40 is in its compressed state, the connecting member 48 has a length of L2, which is less than the length L1 when the connecting member 48 is in its expanded state. When the connecting member 48 is in the compressed state, its alternating curves have a higher amplitude and a smaller wavelength than when it is in the expanded state (compare FIGS. 4A and 4B). Thus, the difference between L2 and L1 compensates for the difference between l1 and l2 of the struts 42, 44 at both ends of the connecting member 48. The lines 70 and 72 in FIGS. 4A and 4B also show that the relevant portion of the stent 40 does not experience any foreshortening, and the lines 74 and 76 in FIGS. 6A and 6B show that the entire stent 40 maintains a consistent length through all its states.
  • Although the connecting members 48 have been described in FIGS. 4A, 4B, 5A and 5B as assuming a particular configuration, it will be appreciated by those skilled in the art that the connecting members 48 can assume other configurations without departing from the spirit and scope of the present invention. For example, the connecting members 48 can be provided in any curved, partially curved, or other configuration as long as they function to compensate for the foreshortening experienced by the longitudinal component of each strut 42 and 44.
  • FIG. 7 illustrates a non-limiting second preferred embodiment of the connecting member, in which the connecting member 48 a has alternating curved segments 80 and straight segments 82. When the connecting member 48 a is compressed, its curved segments 80 also have a higher amplitude and a smaller wavelength than when it is in its expanded state. FIG. 8 illustrates a non-limiting second preferred embodiment, in which the connecting member 48 b has alternating straight segments 84 and 86 that are angled with respect to each other.
  • When the stent 40 is in its fully expanded state, it preferably has an outer diameter that is slightly larger than the inner diameter of the region of the body vessel at which it is to be deployed. This allows the stent 40 to be securely anchored at the desired location and prevents the stent 40 from migrating away from the deployed location.
  • The stent 40 can be provided with varying flexibility or rigidity at different portions or segments along its length to facilitate deployment in body vessels that require such varying flexibility or rigidity. The varying flexibility or rigidity can be accomplished by omitting connecting members 48 and struts 42, 44, or by not connecting one or more struts 32, 44 and/or connecting members 48, thereby creating “gaps” at one or more locations along the stent 40. These locations can be anywhere along the length and/or the circumference of the stent 40. In addition, varying degrees of flexibility in the stent 40 can be accomplished by varying the patterns of these gaps. A non-limiting example would be to provide a substantially spiral pattern of omitted struts 42, 44 and/or connecting members 48, such as illustrated in FIG. 9. The omitted struts 42, 44 and connecting members 48 are illustrated in FIG. 9 in phantom (i.e., the dotted lines) by the numerals 47 (for the struts 42, 44) and 49 (for the connecting members). For example, the omitted struts 47 assume a relatively spiral pattern along the length of the stent 40 from the top left corner of FIG. 9 to the bottom right corner of FIG. 9, and can extend around the circumference of the stent 40. Similarly, the omitted connecting members 49 assume a relatively spiral pattern along the length of the stent 40 from the bottom left corner of FIG. 9 to the top right corner of FIG. 9, and can extend around the circumference of the stent 40.
  • Other non-limiting alternatives include providing such gaps 49 at one or both ends of the stent 40 only, or at a central portion of the stent 40. Further non-limiting alternatives would be to increase the number of these gaps 47, 49 from one or both ends of the stent 40 towards the center of the stent 40, or to increase the number of these gaps 47, 49 from the center of the stent 40 towards one or both ends of the stent 40. It is also possible to omit only a portion of certain connecting members 48 and not the entire ones of these connecting members 48. A portion of the stent 40 having a larger number of gaps 47, 49 would have greater flexibility or reduced rigidity.
  • As a result of the omitted struts 47′, it is possible that some of the annular elements that are made up of the alternating struts 42, 44 may be closed or constitute completely connected annular elements, while some of these annular elements will be open annular elements.
  • The varying flexibility or rigidity can also be accomplished by providing a structural configuration where the size of the open areas or apertures 78 (for example, see FIGS. 4A and 10) defined between the struts 42, 44 and the connecting members 48 is varied at different portions or segments of the stent 40, along the length and/or circumference of the stent 40. In a non-limiting embodiment, all the apertures 78 in one segment of the stent 40 have substantially the same first size, and all the apertures 78 in another segment of the stent 40 have substantially the same second size, the first and second sizes being different. Additional segments, each having apertures 78 with substantially the same size as the other apertures 78 in that segment but having a different size as the apertures 78 in other segments, can also be provided.
  • Varying the size of apertures 78 can be accomplished by varying the lengths of the struts 42, 44 and the connecting members 48. For example, a smaller aperture 78 can be provided by shortening the lengths of the struts 42, 44 and the connecting members 48 that define the particular open area 78. Portions of the stent 40 with smaller apertures 78 are more rigid and less flexible than portions of the stent 40 with larger apertures 78. This allows the stent 40 to be deployed in body vessels that require a stent to be more rigid at one end, and to be increasingly flexible from the rigid end. Examples of such body vessels include the renal and iliac arteries discussed above.
  • Varying the sizes of the apertures 78 also serves other important purposes. For example, providing smaller apertures 78 at the opposing ends of the stent 40 provides increased or closer coverage of the vessel wall, thereby improving support of the diseased vessel wall and preventing fragments of the plaque from being dislodged as embolic debris. The dislodgement of debris can be dangerous in certain vessels, such as the carotid arteries, where dislodged debris can be carried to the brain, possibly resulting in a stroke. As another example, providing larger apertures 78 at central portions of the stent 40 provides wider open areas that may be important in preventing the obstruction of side branches of other body vessels. These wider open areas also allow the passage of guidewires, catheters, stents, grafts, and other deployment devices through the body of the stent 40 into these side branches.
  • The stent 40 can also be provided in a manner in which it assumes a constant diameter in its compressed state, but in which different portions of the stent 40 can assume different diameters when in their fully expanded states. Providing an expandable stent 40 with the capability of assuming different diameters at different portions is important where the stent 40 is used in certain body vessels or branches of body vessels where the lumen diameters may vary. Examples of such body vessels and branches include the carotid and iliac arteries discussed above, and the esophagus.
  • The varying stent diameter can be provided in a number of ways. A first non-limiting alternative is to provide a gradually tapered configuration of the stent 40 a, as shown in FIG. 11A. A tapered configuration is best-suited for use in body vessels which experience a gradual narrowing. A second non-limiting alternative is to provide an abrupt transition, such as a stepped configuration, between two stent segments 30 each having a relatively consistent, but different, diameter. The step can be for a step-up 40 c, as shown in FIG. 1C, or for a step-down 40 b, as shown in FIG. 11B. In addition, a stent 40 can be provided with several changes in diameter along its length to match specific anatomical requirements.
  • The tapering or transitioning of the stent configuration can be accomplished by pre-shaping, and can be enhanced by variations in (1) the thickness of the stent material, (2) the size of apertures 78, and (3) the gaps 47, 49.
  • In addition to the above, it will be appreciated by those skilled in the art that varying flexibility and rigidity can also be accomplished by varying the width or thickness of the stent material at certain locations along the length and/or circumference of the stent 40.
  • A number of materials can be used for both the stent 40 and its struts 42, 44 and connecting members 48, depending on its method of deployment. If used as a self-expanding stent, the stent 40 (including its struts 42, 44 and connecting members 48) is preferably made of a shape memory superelastic metal alloy such as Nitinol, which has the unusual property of “mechanical” memory and trainability. This alloy can be formed into a first predetermined shape above a transition temperature range. The alloy may be plastically deformed into a second shape below the transition temperature range, but the alloy will completely recover to its original (first predetermined) shape when raised back above the transition temperature range. The Nitinol preferably has a composition of about 50% nickel and about 50% titanium. The properties of shape memory alloys such as Nitinol and their use in stents have been well-documented in the literature, and reference can be made to the article by T. W. Duerig, A. R. Pelton and D. Stockel entitled “The Use of Superelasticity in Medicine”, a copy of which is attached hereto and specifically incorporated into this specification by specific reference thereto as though fully set forth herein.
  • Alternatively, the stent 40 (including its struts 42, 44 and connecting members 48) can be made of stainless steel, tantalum, titanium, elgiloy, gold, platinum, or any other metal or alloy, or polymers or composites, having sufficient biocompatibility, rigidity, flexibility, radial strength, radiopacity and antithrombogenicity.
  • Although the connecting members 48 have been described above as having the same material as the struts 42, 44, it is possible to provide the connecting members 48 with a different material without departing from the spirit and scope of the present invention. Such a material should be springy in nature and should allow the connecting members 48 to be compressed and expanded in the longitudinal direction to compensate for the foreshortening experienced by the struts 42 and 44. Non-limiting examples of such materials can include any of the materials described above for the stent 40.
  • 2. Methods of Manufacture
  • The stent 40 can be made from one of a number of methods, depending on the material of the stent 40 and the desired nature of deployment.
  • In a non-limiting first preferred method, the stent 40 is fabricated from a solid Nitinol tube with dimensions that are identical to the stent 40 when it is in the fully compressed state. The pattern of the stent 40 (i.e., its struts 42, 44 and connecting members 48) is programmed into a computer-guided laser cutter or lathe which cuts out the segments between the struts 42, 44 and the connecting members 48 in a manner which closely controls the outside diameter and wall thickness of the stent 40.
  • After the cutting step, the stent 40 is progressively expanded until it reaches its fully expanded state. The expansion can be performed by an internal expansion fixture, although other expansion apparatus and methods can be used without departing from the spirit and scope of the present invention. The overall length of the stent 40 must be consistently maintained throughout the expansion of the stent 40 from its fully compressed to its fully expanded states.
  • Once the stent 40 has been expanded to its fully expanded state, it is heat-treated to “set” the shape memory of the Nitinol material to the fully expanded dimensions. The stent 40 is then cleaned and electro-polished.
  • The next step is to compress the stent 40 again into a dimension which allows for delivery into a vessel, either through percutaneous delivery or through minimally invasive surgical procedures. Specifically, the stent 40 must be compressed into a smaller state so that it can be delivered by a delivery device to the desired location of the vessel. Any conventional delivery device could be used, such as but not limited to a tube, catheter, or sheath. This compression is accomplished by cooling the stent 40 to a low temperature, for example, zero degrees Celcius, and while maintaining this temperature, compressing the stent 40 to allow the stent 40 to be inserted inside the delivery device. Once inserted inside the delivery device, the stent 40 is held by the delivery device in the compressed state at room temperature.
  • In a non-limiting second preferred method, a balloon-expandable stent 40 can be fabricated by connecting a plurality of wires that have been bent or formed into the desired shapes for the struts 42, 44 and connecting members 48. The connection can be accomplished by welding, tying, bonding, or any other conventional method. Alternatively, wire electro-discharge machining can be used. The wires are capable of experiencing plastic deformation when the stent 40 is compressed, and when the stent 40 is expanded. Upon plastic deformation of the stent 40 to either the compressed or the expanded state, the stent 40 remains in this state until another force is applied to plastically deform the stent 40 again.
  • While certain methods of manufacture have been described above, it will be appreciated by those skilled in the art that other methods of manufacture can be utilized without departing from the spirit and scope of the present invention.
  • 3. Deployment Methods
  • The stent 40 can be deployed by a number of delivery systems and delivery methods. These delivery systems and methods will vary depending on whether the stent 40 is expanded by self-expansion, radial expansion forces, or radio frequency.
  • While the description above refers to particular embodiments of the present invention, it will be understood that many modifications may be made without departing from the spirit thereof. The accompanying claims are intended to cover such modifications as would fall within the true scope and spirit of the present invention.

Claims (21)

1-32. (canceled)
33. A stent comprising:
a first annular element, a second annular element disposed axially adjacent to the first annular element, and a third annular element disposed axially adjacent to the second annular element,
each annular element includes a plurality of alternating struts and apices,
wherein at least one connection location joins adjacent annular elements, and the number of connection locations between adjacent annular elements varies along at least a portion of a length of the stent.
34. The stent of claim 33, wherein the number of connection locations between first and second annular elements is different than the number of connection locations between second and third annular elements.
35. The stent of claim 33, wherein the first annular element is disposed at an end of the stent.
36. The stent of claim 33, wherein the connection location includes a connecting member.
37. The stent of claim 36, wherein at least a portion of the connecting member is non-linear.
38. The stent of claim 33, wherein at least a portion of the stent has a varying flexibility.
39. The stent of claim 33, wherein a first portion of the stent has a diameter greater than a second portion of the stent.
40. The stent of claim 39, wherein a portion of the stent has a tapered configuration along the length of the stent.
41. The stent of claim 33, wherein at least a portion thereof has a varying rigidity.
42. The stent of claim 33, wherein the struts of at least one annular element have a varying width or thickness.
43. The stent of claim 33, wherein the stent includes at least one aperture disposed along the length of the stent.
44. The stent of claim 43, wherein a plurality of apertures of a varied size or shape are disposed along the length of the stent.
45. The stent of claim 43, wherein the at least one aperture is disposed in a central portion of the stent.
46. The stent of claim 36, wherein the connecting member can be made of the same material as the annular elements.
47. The stent of claim 46, wherein the stent is made of a metal, metal-alloy, or polymer.
48. The stent of claim 46, wherein the stent is made of shape-memory material.
49. The stent of claim 33, wherein a coating material is applied to the stent.
50. The stent of claim 33, wherein the stent includes a radiopaque material.
51. The stent of claim 50, wherein the radiopaque material can include tantalum or gold.
52. The stent of claim 33, wherein the stent is balloon expandable, or self-expandable.
US11/726,430 1997-02-07 2007-03-21 Non-foreshortening intraluminal prosthesis Abandoned US20070213806A1 (en)

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US08/797,814 US5827321A (en) 1997-02-07 1997-02-07 Non-Foreshortening intraluminal prosthesis
US09/179,021 US6106548A (en) 1997-02-07 1998-10-26 Non-foreshortening intraluminal prosthesis
US09/641,121 US6475236B1 (en) 1997-02-07 2000-08-17 Non-foreshortening intraluminal prosthesis
US10/283,957 US6764506B2 (en) 1997-02-07 2002-10-30 Non-foreshortening intraluminal prosthesis
US10/892,718 US20040267350A1 (en) 2002-10-30 2004-07-16 Non-foreshortening intraluminal prosthesis
US11/726,430 US20070213806A1 (en) 1997-02-07 2007-03-21 Non-foreshortening intraluminal prosthesis

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US09/179,021 Expired - Lifetime US6106548A (en) 1997-02-07 1998-10-26 Non-foreshortening intraluminal prosthesis
US09/641,121 Expired - Lifetime US6475236B1 (en) 1997-02-07 2000-08-17 Non-foreshortening intraluminal prosthesis
US10/283,957 Expired - Lifetime US6764506B2 (en) 1997-02-07 2002-10-30 Non-foreshortening intraluminal prosthesis
US11/726,430 Abandoned US20070213806A1 (en) 1997-02-07 2007-03-21 Non-foreshortening intraluminal prosthesis
US11/726,660 Expired - Fee Related US8882823B2 (en) 1997-02-07 2007-03-21 Non-foreshortening intraluminal prosthesis
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US09/179,021 Expired - Lifetime US6106548A (en) 1997-02-07 1998-10-26 Non-foreshortening intraluminal prosthesis
US09/641,121 Expired - Lifetime US6475236B1 (en) 1997-02-07 2000-08-17 Non-foreshortening intraluminal prosthesis
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Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060149351A1 (en) * 2002-09-02 2006-07-06 Amie Smirthwaite Flexible stent-graft
US10271977B2 (en) 2017-09-08 2019-04-30 Vesper Medical, Inc. Hybrid stent
US10500078B2 (en) 2018-03-09 2019-12-10 Vesper Medical, Inc. Implantable stent
US10702405B2 (en) 2016-03-31 2020-07-07 Vesper Medical, Inc. Intravascular implants
US10849769B2 (en) 2017-08-23 2020-12-01 Vesper Medical, Inc. Non-foreshortening stent
US11357650B2 (en) 2019-02-28 2022-06-14 Vesper Medical, Inc. Hybrid stent
US11364134B2 (en) 2018-02-15 2022-06-21 Vesper Medical, Inc. Tapering stent
US11628076B2 (en) 2017-09-08 2023-04-18 Vesper Medical, Inc. Hybrid stent

Families Citing this family (505)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6582461B1 (en) * 1994-05-19 2003-06-24 Scimed Life Systems, Inc. Tissue supporting devices
CA2186029C (en) * 1995-03-01 2003-04-08 Brian J. Brown Improved longitudinally flexible expandable stent
US7204848B1 (en) * 1995-03-01 2007-04-17 Boston Scientific Scimed, Inc. Longitudinally flexible expandable stent
US6602281B1 (en) * 1995-06-05 2003-08-05 Avantec Vascular Corporation Radially expansible vessel scaffold having beams and expansion joints
US5702418A (en) * 1995-09-12 1997-12-30 Boston Scientific Corporation Stent delivery system
IL124037A (en) 1995-10-13 2003-01-12 Transvascular Inc Device and system for interstitial transvascular intervention
US5776161A (en) 1995-10-16 1998-07-07 Instent, Inc. Medical stents, apparatus and method for making same
EP0932426A4 (en) 1996-02-02 2003-07-30 Transvascular Inc Methods and apparatus for connecting openings formed in adjacent blood vessels or other anatomical structures
US6796997B1 (en) 1996-03-05 2004-09-28 Evysio Medical Devices Ulc Expandable stent
CA2192520A1 (en) 1996-03-05 1997-09-05 Ian M. Penn Expandable stent and method for delivery of same
EP1477133B9 (en) 1996-03-05 2007-11-21 Evysio Medical Devices Ulc Expandable stent
US5868780A (en) * 1996-03-22 1999-02-09 Lashinski; Robert D. Stents for supporting lumens in living tissue
JP4636634B2 (en) 1996-04-26 2011-02-23 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 Intravascular stent
US6235053B1 (en) 1998-02-02 2001-05-22 G. David Jang Tubular stent consists of chevron-shape expansion struts and contralaterally attached diagonal connectors
US20040106985A1 (en) 1996-04-26 2004-06-03 Jang G. David Intravascular stent
US6241760B1 (en) * 1996-04-26 2001-06-05 G. David Jang Intravascular stent
US7686846B2 (en) 1996-06-06 2010-03-30 Devax, Inc. Bifurcation stent and method of positioning in a body lumen
US7238197B2 (en) 2000-05-30 2007-07-03 Devax, Inc. Endoprosthesis deployment system for treating vascular bifurcations
US8728143B2 (en) * 1996-06-06 2014-05-20 Biosensors International Group, Ltd. Endoprosthesis deployment system for treating vascular bifurcations
US6666883B1 (en) 1996-06-06 2003-12-23 Jacques Seguin Endoprosthesis for vascular bifurcation
US6432127B1 (en) 1996-10-11 2002-08-13 Transvascular, Inc. Devices for forming and/or maintaining connections between adjacent anatomical conduits
ES2251763T3 (en) 1997-01-24 2006-05-01 Paragon Intellectual Properties, Llc BISTABLE SPRING STRUCTURE FOR AN ENDOPROTESIS.
US8353948B2 (en) * 1997-01-24 2013-01-15 Celonova Stent, Inc. Fracture-resistant helical stent incorporating bistable cells and methods of use
US8663311B2 (en) 1997-01-24 2014-03-04 Celonova Stent, Inc. Device comprising biodegradable bistable or multistable cells and methods of use
US5827321A (en) * 1997-02-07 1998-10-27 Cornerstone Devices, Inc. Non-Foreshortening intraluminal prosthesis
US20040267350A1 (en) * 2002-10-30 2004-12-30 Roubin Gary S. Non-foreshortening intraluminal prosthesis
DE29702671U1 (en) 1997-02-17 1997-04-10 Jomed Implantate GmbH, 72414 Rangendingen Stent
US20020133222A1 (en) * 1997-03-05 2002-09-19 Das Gladwin S. Expandable stent having a plurality of interconnected expansion modules
US6033433A (en) * 1997-04-25 2000-03-07 Scimed Life Systems, Inc. Stent configurations including spirals
US6451049B2 (en) * 1998-04-29 2002-09-17 Sorin Biomedica Cardio, S.P.A. Stents for angioplasty
IT1292295B1 (en) * 1997-04-29 1999-01-29 Sorin Biomedica Cardio Spa ANGIOPLASTIC STENT
EP0876805B2 (en) 1997-05-07 2010-04-07 Cordis Corporation Intravascular stent and stent delivery system for ostial vessel obstructions
DE29708879U1 (en) * 1997-05-20 1997-07-31 Jomed Implantate GmbH, 72414 Rangendingen Coronary stent
US5836966A (en) 1997-05-22 1998-11-17 Scimed Life Systems, Inc. Variable expansion force stent
EP0884029B1 (en) * 1997-06-13 2004-12-22 Gary J. Becker Expandable intraluminal endoprosthesis
ES2214600T3 (en) * 1997-06-30 2004-09-16 Medex Holding Gmbh INTRALUMINAL IMPLANT.
DE19834956B9 (en) * 1997-08-01 2005-10-20 Eckhard Alt Supporting prosthesis (stent)
EP0898947A3 (en) * 1997-08-15 1999-09-08 GRIESHABER & CO. AG SCHAFFHAUSEN Method and apparatus to improve the outflow of the aqueous humor of an eye
US6890546B2 (en) 1998-09-24 2005-05-10 Abbott Laboratories Medical devices containing rapamycin analogs
US6013091A (en) * 1997-10-09 2000-01-11 Scimed Life Systems, Inc. Stent configurations
US6309414B1 (en) * 1997-11-04 2001-10-30 Sorin Biomedica Cardio S.P.A. Angioplasty stents
US6533807B2 (en) * 1998-02-05 2003-03-18 Medtronic, Inc. Radially-expandable stent and delivery system
US6395019B2 (en) 1998-02-09 2002-05-28 Trivascular, Inc. Endovascular graft
US5931866A (en) * 1998-02-24 1999-08-03 Frantzen; John J. Radially expandable stent featuring accordion stops
US5938697A (en) * 1998-03-04 1999-08-17 Scimed Life Systems, Inc. Stent having variable properties
US6179868B1 (en) * 1998-03-27 2001-01-30 Janet Burpee Stent with reduced shortening
DE69935716T2 (en) * 1998-05-05 2007-08-16 Boston Scientific Ltd., St. Michael STENT WITH SMOOTH ENDS
DE19822157B4 (en) * 1998-05-16 2013-01-10 Abbott Laboratories Vascular Enterprises Ltd. Radially expandable stent for implantation in a body vessel
DE69933560T2 (en) * 1998-06-19 2007-08-30 Endologix, Inc., Irvine SELF-EXPANDING, CRUSHING, ENOVOVASCULAR PROSTHESIS
US6261319B1 (en) * 1998-07-08 2001-07-17 Scimed Life Systems, Inc. Stent
US6461380B1 (en) 1998-07-28 2002-10-08 Advanced Cardiovascular Systems, Inc. Stent configuration
US6682554B2 (en) 1998-09-05 2004-01-27 Jomed Gmbh Methods and apparatus for a stent having an expandable web structure
US7815763B2 (en) 2001-09-28 2010-10-19 Abbott Laboratories Vascular Enterprises Limited Porous membranes for medical implants and methods of manufacture
DE19840645A1 (en) 1998-09-05 2000-03-09 Jomed Implantate Gmbh Stent
US6755856B2 (en) 1998-09-05 2004-06-29 Abbott Laboratories Vascular Enterprises Limited Methods and apparatus for stenting comprising enhanced embolic protection, coupled with improved protection against restenosis and thrombus formation
US20020019660A1 (en) * 1998-09-05 2002-02-14 Marc Gianotti Methods and apparatus for a curved stent
US7887578B2 (en) 1998-09-05 2011-02-15 Abbott Laboratories Vascular Enterprises Limited Stent having an expandable web structure
US6193744B1 (en) * 1998-09-10 2001-02-27 Scimed Life Systems, Inc. Stent configurations
US7960405B2 (en) * 1998-09-24 2011-06-14 Abbott Laboratories Compounds and methods for treatment and prevention of diseases
US6042597A (en) 1998-10-23 2000-03-28 Scimed Life Systems, Inc. Helical stent design
US6733523B2 (en) 1998-12-11 2004-05-11 Endologix, Inc. Implantable vascular graft
US6187036B1 (en) 1998-12-11 2001-02-13 Endologix, Inc. Endoluminal vascular prosthesis
US6660030B2 (en) 1998-12-11 2003-12-09 Endologix, Inc. Bifurcation graft deployment catheter
CA2350499C (en) 1998-12-11 2008-01-29 Endologix, Inc. Endoluminal vascular prosthesis
US6743252B1 (en) 1998-12-18 2004-06-01 Cook Incorporated Cannula stent
US6355057B1 (en) 1999-01-14 2002-03-12 Medtronic, Inc. Staggered endoluminal stent
US6251134B1 (en) * 1999-02-28 2001-06-26 Inflow Dynamics Inc. Stent with high longitudinal flexibility
US6261316B1 (en) 1999-03-11 2001-07-17 Endologix, Inc. Single puncture bifurcation graft deployment system
US6273910B1 (en) 1999-03-11 2001-08-14 Advanced Cardiovascular Systems, Inc. Stent with varying strut geometry
US8034100B2 (en) 1999-03-11 2011-10-11 Endologix, Inc. Graft deployment system
DE19913978A1 (en) * 1999-03-18 2000-09-28 Schering Ag Asymmetric stent containing irregularly distributed active agents or radioisotopes useful e.g. for treating atherosclerosis and preventing restenosis
US6464723B1 (en) * 1999-04-22 2002-10-15 Advanced Cardiovascular Systems, Inc. Radiopaque stents
US6273911B1 (en) 1999-04-22 2001-08-14 Advanced Cardiovascular Systems, Inc. Variable strength stent
US6245101B1 (en) 1999-05-03 2001-06-12 William J. Drasler Intravascular hinge stent
US8016873B1 (en) 1999-05-03 2011-09-13 Drasler William J Intravascular hinge stent
US6375676B1 (en) 1999-05-17 2002-04-23 Advanced Cardiovascular Systems, Inc. Self-expanding stent with enhanced delivery precision and stent delivery system
US6997951B2 (en) * 1999-06-30 2006-02-14 Edwards Lifesciences Ag Method and device for treatment of mitral insufficiency
US6409754B1 (en) * 1999-07-02 2002-06-25 Scimed Life Systems, Inc. Flexible segmented stent
US6569193B1 (en) 1999-07-22 2003-05-27 Advanced Cardiovascular Systems, Inc. Tapered self-expanding stent
US6544279B1 (en) 2000-08-09 2003-04-08 Incept, Llc Vascular device for emboli, thrombus and foreign body removal and methods of use
DE19937638B4 (en) * 1999-08-12 2006-11-02 Alveolus Inc. Tracheal Stent
US6371980B1 (en) * 1999-08-30 2002-04-16 Cardiovasc, Inc. Composite expandable device with impervious polymeric covering and bioactive coating thereon, delivery apparatus and method
US6293968B1 (en) 1999-09-02 2001-09-25 Syde A. Taheri Inflatable intraluminal vascular stent
US20010047200A1 (en) * 1999-10-13 2001-11-29 Raymond Sun Non-foreshortening intraluminal prosthesis
US6585758B1 (en) 1999-11-16 2003-07-01 Scimed Life Systems, Inc. Multi-section filamentary endoluminal stent
US6610087B1 (en) 1999-11-16 2003-08-26 Scimed Life Systems, Inc. Endoluminal stent having a matched stiffness region and/or a stiffness gradient and methods for providing stent kink resistance
US6361555B1 (en) 1999-12-15 2002-03-26 Advanced Cardiovascular Systems, Inc. Stent and stent delivery assembly and method of use
US6443979B1 (en) 1999-12-20 2002-09-03 Advanced Cardiovascular Systems, Inc. Expandable stent delivery sheath and method of use
US6423090B1 (en) 2000-02-11 2002-07-23 Advanced Cardiovascular Systems, Inc. Stent pattern with staged expansion
US7758627B2 (en) * 2000-03-01 2010-07-20 Medinol, Ltd. Longitudinally flexible stent
US7828835B2 (en) 2000-03-01 2010-11-09 Medinol Ltd. Longitudinally flexible stent
US7141062B1 (en) * 2000-03-01 2006-11-28 Medinol, Ltd. Longitudinally flexible stent
US8496699B2 (en) * 2000-03-01 2013-07-30 Medinol Ltd. Longitudinally flexible stent
US8202312B2 (en) * 2000-03-01 2012-06-19 Medinol Ltd. Longitudinally flexible stent
US8920487B1 (en) 2000-03-01 2014-12-30 Medinol Ltd. Longitudinally flexible stent
US6723119B2 (en) * 2000-03-01 2004-04-20 Medinol Ltd. Longitudinally flexible stent
US7621947B2 (en) * 2000-03-01 2009-11-24 Medinol, Ltd. Longitudinally flexible stent
EP1132058A1 (en) * 2000-03-06 2001-09-12 Advanced Laser Applications Holding S.A. Intravascular prothesis
US6520984B1 (en) 2000-04-28 2003-02-18 Cardiovasc, Inc. Stent graft assembly and method
US20030114918A1 (en) * 2000-04-28 2003-06-19 Garrison Michi E. Stent graft assembly and method
US6451050B1 (en) 2000-04-28 2002-09-17 Cardiovasc, Inc. Stent graft and method
US6616689B1 (en) 2000-05-03 2003-09-09 Advanced Cardiovascular Systems, Inc. Intravascular stent
US6602282B1 (en) * 2000-05-04 2003-08-05 Avantec Vascular Corporation Flexible stent structure
US7169175B2 (en) 2000-05-22 2007-01-30 Orbusneich Medical, Inc. Self-expanding stent
US7632303B1 (en) 2000-06-07 2009-12-15 Advanced Cardiovascular Systems, Inc. Variable stiffness medical devices
US6652576B1 (en) 2000-06-07 2003-11-25 Advanced Cardiovascular Systems, Inc. Variable stiffness stent
US6652579B1 (en) 2000-06-22 2003-11-25 Advanced Cardiovascular Systems, Inc. Radiopaque stent
US6799637B2 (en) 2000-10-20 2004-10-05 Schlumberger Technology Corporation Expandable tubing and method
DE10040630A1 (en) * 2000-08-16 2002-03-07 Thomas Hupp Stent for implantation in the carotid artery
US7766956B2 (en) 2000-09-22 2010-08-03 Boston Scientific Scimed, Inc. Intravascular stent and assembly
US6669722B2 (en) * 2000-09-22 2003-12-30 Cordis Corporation Stent with optimal strength and radiopacity characteristics
US6695833B1 (en) 2000-09-27 2004-02-24 Nellix, Inc. Vascular stent-graft apparatus and forming method
AU2002233936A1 (en) * 2000-11-07 2002-05-21 Advanced Bio Prosthetic Surfaces, Ltd. Endoluminal stent, self-fupporting endoluminal graft and methods of making same
US6929660B1 (en) 2000-12-22 2005-08-16 Advanced Cardiovascular Systems, Inc. Intravascular stent
NO335594B1 (en) 2001-01-16 2015-01-12 Halliburton Energy Serv Inc Expandable devices and methods thereof
US6998060B2 (en) 2001-03-01 2006-02-14 Cordis Corporation Flexible stent and method of manufacture
US6679911B2 (en) 2001-03-01 2004-01-20 Cordis Corporation Flexible stent
JP4667716B2 (en) * 2001-03-13 2011-04-13 リヒター,ヨラム Stent-type expansion method and apparatus
DE10118944B4 (en) 2001-04-18 2013-01-31 Merit Medical Systems, Inc. Removable, essentially cylindrical implants
US6749628B1 (en) 2001-05-17 2004-06-15 Advanced Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US20040176837A1 (en) * 2001-05-17 2004-09-09 Atladottir Svava Maria Self-expanding stent and catheter assembly and method for treating bifurcations
US7087088B2 (en) * 2001-05-24 2006-08-08 Torax Medical, Inc. Methods and apparatus for regulating the flow of matter through body tubing
US6629994B2 (en) * 2001-06-11 2003-10-07 Advanced Cardiovascular Systems, Inc. Intravascular stent
US6939373B2 (en) 2003-08-20 2005-09-06 Advanced Cardiovascular Systems, Inc. Intravascular stent
US6818013B2 (en) * 2001-06-14 2004-11-16 Cordis Corporation Intravascular stent device
US6673106B2 (en) * 2001-06-14 2004-01-06 Cordis Neurovascular, Inc. Intravascular stent device
GB0114918D0 (en) * 2001-06-19 2001-08-08 Vortex Innovation Ltd Devices for repairing aneurysms
US6635083B1 (en) 2001-06-25 2003-10-21 Advanced Cardiovascular Systems, Inc. Stent with non-linear links and method of use
US20030109886A1 (en) 2001-06-27 2003-06-12 Martin Keegan Catheter
US6749629B1 (en) 2001-06-27 2004-06-15 Advanced Cardiovascular Systems, Inc. Stent pattern with figure-eights
CA2449981A1 (en) 2001-06-27 2003-01-09 Salviac Limited A catheter
WO2003009773A2 (en) 2001-07-26 2003-02-06 Alveolus Inc. Removable stent and method of using the same
IES20010828A2 (en) * 2001-09-12 2003-03-19 Medtronic Inc Medical device for intraluminal endovascular stenting
EP1293177B1 (en) * 2001-09-18 2005-03-02 Abbott Laboratories Vascular Enterprises Limited Stent
US8262689B2 (en) * 2001-09-28 2012-09-11 Advanced Cardiovascular Systems, Inc. Embolic filtering devices
US20040111108A1 (en) 2001-11-09 2004-06-10 Farnan Robert C. Balloon catheter with non-deployable stent
DE60231733D1 (en) * 2001-11-09 2009-05-07 Angioscore Inc
US6776794B1 (en) 2001-11-28 2004-08-17 Advanced Cardiovascular Systems, Inc. Stent pattern with mirror image
EP1917931A3 (en) 2001-12-03 2013-02-27 Intek Technology LLC Multi-segment modular stent and methods for manufacturing stents
US20030176914A1 (en) * 2003-01-21 2003-09-18 Rabkin Dmitry J. Multi-segment modular stent and methods for manufacturing stents
US7147661B2 (en) * 2001-12-20 2006-12-12 Boston Scientific Santa Rosa Corp. Radially expandable stent
US6964681B2 (en) * 2002-01-29 2005-11-15 Medtronic Vascular, Inc. Flared stent and method of use
US7291165B2 (en) 2002-01-31 2007-11-06 Boston Scientific Scimed, Inc. Medical device for delivering biologically active material
US7326245B2 (en) * 2002-01-31 2008-02-05 Boston Scientific Scimed, Inc. Medical device for delivering biologically active material
US7445629B2 (en) * 2002-01-31 2008-11-04 Boston Scientific Scimed, Inc. Medical device for delivering biologically active material
JP4512369B2 (en) * 2002-01-31 2010-07-28 ラディ・メディカル・システムズ・アクチェボラーグ Stent
US20050197715A1 (en) * 2002-04-26 2005-09-08 Torax Medical, Inc. Methods and apparatus for implanting devices into non-sterile body lumens or organs
US7695427B2 (en) 2002-04-26 2010-04-13 Torax Medical, Inc. Methods and apparatus for treating body tissue sphincters and the like
US7637935B2 (en) 2002-05-06 2009-12-29 Abbott Laboratories Endoprosthesis for controlled contraction and expansion
WO2003094798A1 (en) 2002-05-08 2003-11-20 Abbott Laboratories Endoprosthesis having foot extensions
US8303617B2 (en) * 2002-05-13 2012-11-06 Salviac Limited Embolic protection system
US7195648B2 (en) 2002-05-16 2007-03-27 Cordis Neurovascular, Inc. Intravascular stent device
EP1506793B1 (en) * 2002-05-20 2009-08-05 Kawasumi Laboratories, Inc. Stent and stent graft
US6656220B1 (en) 2002-06-17 2003-12-02 Advanced Cardiovascular Systems, Inc. Intravascular stent
US8425549B2 (en) 2002-07-23 2013-04-23 Reverse Medical Corporation Systems and methods for removing obstructive matter from body lumens and treating vascular defects
US6878162B2 (en) * 2002-08-30 2005-04-12 Edwards Lifesciences Ag Helical stent having improved flexibility and expandability
US9561123B2 (en) 2002-08-30 2017-02-07 C.R. Bard, Inc. Highly flexible stent and method of manufacture
US20040054398A1 (en) * 2002-09-13 2004-03-18 Cully Edward H. Stent device with multiple helix construction
EP1542616B1 (en) 2002-09-20 2015-04-22 Endologix, Inc. Stent-graft with positioning anchor
US20040093056A1 (en) 2002-10-26 2004-05-13 Johnson Lianw M. Medical appliance delivery apparatus and method of use
US20040087886A1 (en) * 2002-10-30 2004-05-06 Scimed Life Systems, Inc. Linearly expandable ureteral stent
US7959671B2 (en) 2002-11-05 2011-06-14 Merit Medical Systems, Inc. Differential covering and coating methods
US7875068B2 (en) 2002-11-05 2011-01-25 Merit Medical Systems, Inc. Removable biliary stent
US7527644B2 (en) 2002-11-05 2009-05-05 Alveolus Inc. Stent with geometry determinated functionality and method of making the same
US7637942B2 (en) 2002-11-05 2009-12-29 Merit Medical Systems, Inc. Coated stent with geometry determinated functionality and method of making the same
US7208190B2 (en) 2002-11-07 2007-04-24 Abbott Laboratories Method of loading beneficial agent to a prosthesis by fluid-jet application
EP2074968B1 (en) 2002-11-08 2016-01-27 Jacques Seguin Endoprosthesis for vascular bifurcation
US7316710B1 (en) * 2002-12-30 2008-01-08 Advanced Cardiovascular Systems, Inc. Flexible stent
US6849084B2 (en) * 2002-12-31 2005-02-01 Intek Technology L.L.C. Stent delivery system
US7686824B2 (en) 2003-01-21 2010-03-30 Angioscore, Inc. Apparatus and methods for treating hardened vascular lesions
US8080026B2 (en) 2003-01-21 2011-12-20 Angioscore, Inc. Apparatus and methods for treating hardened vascular lesions
US20050021070A1 (en) * 2003-01-21 2005-01-27 Angioscore, Inc. Methods and apparatus for manipulating vascular prostheses
US7179286B2 (en) * 2003-02-21 2007-02-20 Boston Scientific Scimed, Inc. Stent with stepped connectors
US7025779B2 (en) * 2003-02-26 2006-04-11 Scimed Life Systems, Inc. Endoluminal device having enhanced affixation characteristics
AU2004224415B2 (en) * 2003-03-19 2011-07-14 Vactronix Scientific, Llc Endoluminal stent having mid-interconnecting members
US7637934B2 (en) 2003-03-31 2009-12-29 Merit Medical Systems, Inc. Medical appliance optical delivery and deployment apparatus and method
US7604660B2 (en) 2003-05-01 2009-10-20 Merit Medical Systems, Inc. Bifurcated medical appliance delivery apparatus and method
US7625398B2 (en) 2003-05-06 2009-12-01 Abbott Laboratories Endoprosthesis having foot extensions
US7625401B2 (en) 2003-05-06 2009-12-01 Abbott Laboratories Endoprosthesis having foot extensions
US7112216B2 (en) * 2003-05-28 2006-09-26 Boston Scientific Scimed, Inc. Stent with tapered flexibility
US6916336B2 (en) * 2003-06-09 2005-07-12 Avantec Vascular Corporation Vascular prosthesis
US7131993B2 (en) * 2003-06-25 2006-11-07 Boston Scientific Scimed, Inc. Varying circumferential spanned connectors in a stent
DE10328882B4 (en) * 2003-06-26 2010-06-02 Admedes Schuessler Gmbh Use of a flexible shaft as a hose-like insertion device
DE10335649A1 (en) * 2003-07-30 2005-02-24 Jotec Gmbh Braid stent for implantation in a blood vessel
US7959665B2 (en) * 2003-07-31 2011-06-14 Abbott Cardiovascular Systems Inc. Intravascular stent with inverted end rings
US20080033570A1 (en) * 2003-08-01 2008-02-07 Blitz Benjamin T Prostatic stent placement device
DE10342757A1 (en) * 2003-09-16 2005-04-07 Campus Gmbh & Co. Kg Stent with terminal anchoring elements
US20050149168A1 (en) * 2003-12-30 2005-07-07 Daniel Gregorich Stent to be deployed on a bend
US8454676B1 (en) 2004-01-20 2013-06-04 Advanced Cardiovascular Systems, Inc. Transition matching stent
US8431145B2 (en) 2004-03-19 2013-04-30 Abbott Laboratories Multiple drug delivery from a balloon and a prosthesis
JP4447356B2 (en) * 2004-03-19 2010-04-07 パイオニア株式会社 Speaker device
US20070027523A1 (en) * 2004-03-19 2007-02-01 Toner John L Method of treating vascular disease at a bifurcated vessel using coated balloon
EP1735042B1 (en) 2004-03-19 2011-11-23 Abbott Laboratories Multiple drug delivery from a balloon and a prosthesis
US20100030183A1 (en) * 2004-03-19 2010-02-04 Toner John L Method of treating vascular disease at a bifurcated vessel using a coated balloon
US7686825B2 (en) 2004-03-25 2010-03-30 Hauser David L Vascular filter device
DE102004022044B4 (en) * 2004-05-03 2008-12-18 Qualimed Innovative Medizinprodukte Gmbh stent
US20060122693A1 (en) * 2004-05-10 2006-06-08 Youssef Biadillah Stent valve and method of manufacturing same
US20060122692A1 (en) * 2004-05-10 2006-06-08 Ran Gilad Stent valve and method of using same
US20060122686A1 (en) * 2004-05-10 2006-06-08 Ran Gilad Stent and method of manufacturing same
US8048145B2 (en) 2004-07-22 2011-11-01 Endologix, Inc. Graft systems having filling structures supported by scaffolds and methods for their use
US20060074480A1 (en) 2004-09-01 2006-04-06 Pst, Llc Stent and method for manufacturing the stent
US20060064155A1 (en) * 2004-09-01 2006-03-23 Pst, Llc Stent and method for manufacturing the stent
GB0419954D0 (en) 2004-09-08 2004-10-13 Advotek Medical Devices Ltd System for directing therapy
US7927346B2 (en) * 2004-09-10 2011-04-19 Stryker Corporation Diversion device to increase cerebral blood flow
WO2006034436A2 (en) 2004-09-21 2006-03-30 Stout Medical Group, L.P. Expandable support device and method of use
US7887579B2 (en) 2004-09-29 2011-02-15 Merit Medical Systems, Inc. Active stent
JP4203476B2 (en) * 2005-01-24 2009-01-07 シャープ株式会社 Portable information device
FR2881946B1 (en) * 2005-02-17 2008-01-04 Jacques Seguin DEVICE FOR THE TREATMENT OF BODILY CONDUIT AT BIFURCATION LEVEL
EP1868663B1 (en) * 2005-03-23 2011-11-16 Abbott Laboratories Delivery of highly lipophilic agents via medical devices
EP1871292B1 (en) 2005-04-04 2019-10-23 Flexible Stenting Solutions, Inc. Flexible stent
DE102005016103B4 (en) * 2005-04-08 2014-10-09 Merit Medical Systems, Inc. Duodenumstent
US7763198B2 (en) 2005-04-12 2010-07-27 Abbott Cardiovascular Systems Inc. Method for retaining a vascular stent on a catheter
US7947207B2 (en) 2005-04-12 2011-05-24 Abbott Cardiovascular Systems Inc. Method for retaining a vascular stent on a catheter
US8628565B2 (en) * 2005-04-13 2014-01-14 Abbott Cardiovascular Systems Inc. Intravascular stent
DE102005019649A1 (en) * 2005-04-26 2006-11-02 Alveolus Inc. Flexible stent for positioning in lumen of esophagus comprises tube and stabilization members defined circumferentially about tube, where each member extends inwardly in tube to define inner diameter that is less than inner diameter of tube
JP5112295B2 (en) * 2005-04-27 2013-01-09 スタウト メディカル グループ,エル.ピー. Expandable support and method of use
US20060253193A1 (en) * 2005-05-03 2006-11-09 Lichtenstein Samuel V Mechanical means for controlling blood pressure
US10076641B2 (en) 2005-05-11 2018-09-18 The Spectranetics Corporation Methods and systems for delivering substances into luminal walls
US7731654B2 (en) 2005-05-13 2010-06-08 Merit Medical Systems, Inc. Delivery device with viewing window and associated method
EP1895938B1 (en) 2005-06-30 2019-02-20 Abbott Laboratories Endoprosthesis having foot extensions
JP2009500121A (en) 2005-07-07 2009-01-08 ネリックス・インコーポレーテッド System and method for treatment of an intraluminal aneurysm
JP5081822B2 (en) 2005-07-14 2012-11-28 スタウト メディカル グループ,エル.ピー. Expandable support device and system
US20070050011A1 (en) * 2005-08-26 2007-03-01 Medlogics Device Corporation Lumen-supporting stents and methods for creating lumen-supporting stents with various open/closed designs
US8518100B2 (en) * 2005-12-19 2013-08-27 Advanced Cardiovascular Systems, Inc. Drug eluting stent for the treatment of dialysis graft stenoses
US20070173924A1 (en) * 2006-01-23 2007-07-26 Daniel Gelbart Axially-elongating stent and method of deployment
US20070191926A1 (en) * 2006-02-14 2007-08-16 Advanced Cardiovascular Systems, Inc. Stent pattern for high stent retention
MX2008009866A (en) 2006-02-14 2008-10-14 Angiomed Ag Highly flexible stent and method of manufacture.
US8475074B1 (en) 2006-03-01 2013-07-02 Hrl Laboratories, Llc Variable stiffness joint mechanism
US7678440B1 (en) * 2006-03-01 2010-03-16 Mcknight Geoffrey P Deformable variable-stiffness cellular structures
EP2023864B1 (en) 2006-05-01 2019-07-10 Stout Medical Group, L.P. Expandable support device
US20070276444A1 (en) * 2006-05-24 2007-11-29 Daniel Gelbart Self-powered leadless pacemaker
US20070276465A1 (en) * 2006-05-25 2007-11-29 Rosaire Mongrain Stent
US20080097620A1 (en) 2006-05-26 2008-04-24 Nanyang Technological University Implantable article, method of forming same and method for reducing thrombogenicity
WO2007146021A2 (en) 2006-06-06 2007-12-21 Cook Incorporated Stent with a crush-resistant zone
US20070287879A1 (en) * 2006-06-13 2007-12-13 Daniel Gelbart Mechanical means for controlling blood pressure
EP2049039A2 (en) 2006-06-22 2009-04-22 AMS Research Corporation Adjustable tension incontinence sling assemblies
US8029558B2 (en) 2006-07-07 2011-10-04 Abbott Cardiovascular Systems, Inc. Stent and catheter assembly and method for treating bifurcations
US8613698B2 (en) 2006-07-10 2013-12-24 Mcneil-Ppc, Inc. Resilient device
EP2043570B1 (en) 2006-07-10 2018-10-31 First Quality Hygienic, Inc. Resilient device
US7717892B2 (en) 2006-07-10 2010-05-18 Mcneil-Ppc, Inc. Method of treating urinary incontinence
US10004584B2 (en) 2006-07-10 2018-06-26 First Quality Hygienic, Inc. Resilient intravaginal device
US10219884B2 (en) 2006-07-10 2019-03-05 First Quality Hygienic, Inc. Resilient device
US8252041B2 (en) 2006-08-23 2012-08-28 Abbott Laboratories Stent designs for use in peripheral vessels
US7988720B2 (en) * 2006-09-12 2011-08-02 Boston Scientific Scimed, Inc. Longitudinally flexible expandable stent
US20080081064A1 (en) * 2006-09-28 2008-04-03 Surmodics, Inc. Implantable Medical Device with Apertures for Delivery of Bioactive Agents
US8778009B2 (en) 2006-10-06 2014-07-15 Abbott Cardiovascular Systems Inc. Intravascular stent
US9387100B2 (en) 2007-01-08 2016-07-12 Cardinal Health Switzerland GmbH Intraluminal medical device having variable axial flexibility about the circumference of the device
FR2911063B1 (en) 2007-01-09 2009-03-20 Stentys S A S Soc Par Actions RUPTIBLE BRIDGE STRUCTURE FOR STENT, AND STENT INCLUDING SUCH BRIDGE STRUCTURES.
US8523931B2 (en) 2007-01-12 2013-09-03 Endologix, Inc. Dual concentric guidewire and methods of bifurcated graft deployment
US8333799B2 (en) 2007-02-12 2012-12-18 C. R. Bard, Inc. Highly flexible stent and method of manufacture
EP4005537A1 (en) * 2007-02-12 2022-06-01 C.R. Bard Inc. Highly flexible stent and method of manufacture
AT504975B1 (en) * 2007-02-19 2013-12-15 Arc Austrian Res Centers Gmbh GRID PART OF METAL AND METHOD FOR PRODUCING A GRID PART
US8623070B2 (en) 2007-03-08 2014-01-07 Thomas O. Bales Tapered helical stent and method for manufacturing the stent
US8974514B2 (en) 2007-03-13 2015-03-10 Abbott Cardiovascular Systems Inc. Intravascular stent with integrated link and ring strut
DE102007019058A1 (en) 2007-04-23 2008-10-30 Stengel, Max, Dr.Dr. Vascular implant for the treatment of an aneurysm
US20080269746A1 (en) 2007-04-24 2008-10-30 Osteolign, Inc. Conformable intramedullary implant with nestable components
US8016874B2 (en) 2007-05-23 2011-09-13 Abbott Laboratories Vascular Enterprises Limited Flexible stent with elevated scaffolding properties
US8128679B2 (en) 2007-05-23 2012-03-06 Abbott Laboratories Vascular Enterprises Limited Flexible stent with torque-absorbing connectors
US7867273B2 (en) * 2007-06-27 2011-01-11 Abbott Laboratories Endoprostheses for peripheral arteries and other body vessels
US9144508B2 (en) * 2007-07-19 2015-09-29 Back Bay Medical Inc. Radially expandable stent
US8663318B2 (en) * 2007-07-23 2014-03-04 Hocor Cardiovascular Technologies Llc Method and apparatus for percutaneous aortic valve replacement
US8663319B2 (en) 2007-07-23 2014-03-04 Hocor Cardiovascular Technologies Llc Methods and apparatus for percutaneous aortic valve replacement
US7988723B2 (en) 2007-08-02 2011-08-02 Flexible Stenting Solutions, Inc. Flexible stent
US8226701B2 (en) 2007-09-26 2012-07-24 Trivascular, Inc. Stent and delivery system for deployment thereof
US8066755B2 (en) 2007-09-26 2011-11-29 Trivascular, Inc. System and method of pivoted stent deployment
US8663309B2 (en) 2007-09-26 2014-03-04 Trivascular, Inc. Asymmetric stent apparatus and method
EP2194921B1 (en) 2007-10-04 2018-08-29 TriVascular, Inc. Modular vascular graft for low profile percutaneous delivery
US20090105687A1 (en) * 2007-10-05 2009-04-23 Angioscore, Inc. Scoring catheter with drug delivery membrane
US10123803B2 (en) 2007-10-17 2018-11-13 Covidien Lp Methods of managing neurovascular obstructions
US9220522B2 (en) 2007-10-17 2015-12-29 Covidien Lp Embolus removal systems with baskets
US11337714B2 (en) 2007-10-17 2022-05-24 Covidien Lp Restoring blood flow and clot removal during acute ischemic stroke
US8088140B2 (en) 2008-05-19 2012-01-03 Mindframe, Inc. Blood flow restorative and embolus removal methods
US8066757B2 (en) 2007-10-17 2011-11-29 Mindframe, Inc. Blood flow restoration and thrombus management methods
US8585713B2 (en) 2007-10-17 2013-11-19 Covidien Lp Expandable tip assembly for thrombus management
US9198687B2 (en) 2007-10-17 2015-12-01 Covidien Lp Acute stroke revascularization/recanalization systems processes and products thereby
US8926680B2 (en) 2007-11-12 2015-01-06 Covidien Lp Aneurysm neck bridging processes with revascularization systems methods and products thereby
US8083789B2 (en) 2007-11-16 2011-12-27 Trivascular, Inc. Securement assembly and method for expandable endovascular device
US8328861B2 (en) 2007-11-16 2012-12-11 Trivascular, Inc. Delivery system and method for bifurcated graft
US7850726B2 (en) 2007-12-20 2010-12-14 Abbott Laboratories Vascular Enterprises Limited Endoprosthesis having struts linked by foot extensions
US8337544B2 (en) 2007-12-20 2012-12-25 Abbott Laboratories Vascular Enterprises Limited Endoprosthesis having flexible connectors
US8920488B2 (en) 2007-12-20 2014-12-30 Abbott Laboratories Vascular Enterprises Limited Endoprosthesis having a stable architecture
US20090163998A1 (en) * 2007-12-20 2009-06-25 Abbott Laboratories Vascular Enterprises Limited Endoprosthesis having rings linked by foot extensions
US8470021B2 (en) * 2007-12-28 2013-06-25 Cook Medical Technologies Llc Radially expandable stent
KR100988816B1 (en) * 2008-01-29 2010-10-20 신경민 A stent
EP2254485B1 (en) 2008-02-22 2017-08-30 Covidien LP Apparatus for flow restoration
US8221494B2 (en) 2008-02-22 2012-07-17 Endologix, Inc. Apparatus and method of placement of a graft or graft system
US9039748B2 (en) * 2008-04-07 2015-05-26 Abbott Cardiovascular Systems Inc. Method of securing a medical device onto a balloon and system thereof
US8236040B2 (en) 2008-04-11 2012-08-07 Endologix, Inc. Bifurcated graft deployment systems and methods
CN101977650A (en) 2008-04-11 2011-02-16 曼德弗雷姆公司 Monorail neuro-microcatheter for delivery of medical devices to treat stroke, processes and products thereby
EP2278939B1 (en) 2008-04-25 2021-04-14 Endologix LLC Stent graft delivery system
US10716573B2 (en) 2008-05-01 2020-07-21 Aneuclose Janjua aneurysm net with a resilient neck-bridging portion for occluding a cerebral aneurysm
US10028747B2 (en) 2008-05-01 2018-07-24 Aneuclose Llc Coils with a series of proximally-and-distally-connected loops for occluding a cerebral aneurysm
US20090287233A1 (en) * 2008-05-15 2009-11-19 Huculak John C Small Gauge Mechanical Tissue Cutter/Aspirator Probe For Glaucoma Surgery
US20090287143A1 (en) * 2008-05-15 2009-11-19 Casey Line Small Gauge Mechanical Tissue Cutter/Aspirator Probe For Glaucoma Surgery
CA2726596A1 (en) 2008-06-04 2009-12-10 Nellix, Inc. Sealing apparatus and methods of use
US11207199B2 (en) 2008-06-11 2021-12-28 Q3 Medical Devices Limited Stent with anti-migration devices
US10245165B2 (en) 2009-04-02 2019-04-02 Q3 Medical Devices Limited Stent
US10022164B2 (en) 2008-06-11 2018-07-17 Eventions, Llc Orthopedic fastener device
US10117760B2 (en) 2009-04-02 2018-11-06 Q3 Medical Devices Limited Stent
US20100256731A1 (en) 2009-04-02 2010-10-07 Mangiardi Eric K Stent
US10898620B2 (en) * 2008-06-20 2021-01-26 Razmodics Llc Composite stent having multi-axial flexibility and method of manufacture thereof
US8206635B2 (en) 2008-06-20 2012-06-26 Amaranth Medical Pte. Stent fabrication via tubular casting processes
US20100042202A1 (en) * 2008-08-13 2010-02-18 Kamal Ramzipoor Composite stent having multi-axial flexibility
US8206636B2 (en) 2008-06-20 2012-06-26 Amaranth Medical Pte. Stent fabrication via tubular casting processes
EP2520320B1 (en) 2008-07-01 2016-11-02 Endologix, Inc. Catheter system
JP6023427B2 (en) * 2008-07-21 2016-11-09 ジェニファー ケー. ホワイト, Repositionable intraluminal support structure and its application
US9039756B2 (en) 2008-07-21 2015-05-26 Jenesis Surgical, Llc Repositionable endoluminal support structure and its applications
US9402707B2 (en) 2008-07-22 2016-08-02 Neuravi Limited Clot capture systems and associated methods
US9005274B2 (en) 2008-08-04 2015-04-14 Stentys Sas Method for treating a body lumen
US9149376B2 (en) 2008-10-06 2015-10-06 Cordis Corporation Reconstrainable stent delivery system
US9125720B2 (en) 2008-10-13 2015-09-08 Alcon Research, Ltd. Capsularhexis device with flexible heating element
US20100204795A1 (en) 2008-11-12 2010-08-12 Stout Medical Group, L.P. Fixation device and method
US20100211176A1 (en) 2008-11-12 2010-08-19 Stout Medical Group, L.P. Fixation device and method
WO2010065241A1 (en) * 2008-12-02 2010-06-10 Boston Scientific Scimed, Inc. Stent with graduated stiffness
US8137344B2 (en) 2008-12-10 2012-03-20 Alcon Research, Ltd. Flexible, automated capsulorhexis device
US8157797B2 (en) 2009-01-12 2012-04-17 Alcon Research, Ltd. Capsularhexis device with retractable bipolar electrodes
CA2751233C (en) 2009-02-02 2015-06-16 Cordis Corporation Flexible stent design
US20100274276A1 (en) * 2009-04-22 2010-10-28 Ricky Chow Aneurysm treatment system, device and method
BRPI1013573A2 (en) * 2009-04-24 2016-04-12 Flexible Stenting Solutions Inc flexible devices
US20110054586A1 (en) 2009-04-28 2011-03-03 Endologix, Inc. Apparatus and method of placement of a graft or graft system
US10772717B2 (en) 2009-05-01 2020-09-15 Endologix, Inc. Percutaneous method and device to treat dissections
JP2012525239A (en) 2009-05-01 2012-10-22 エンドロジックス、インク Transcutaneous methods and devices for treating dissociation (priority information and incorporation by reference)
US8814854B2 (en) 2009-06-03 2014-08-26 Alcon Research, Ltd. Capsulotomy repair device and method for capsulotomy repair
US20100312252A1 (en) * 2009-06-03 2010-12-09 Guangyao Jia Capsularhexis device with flexible heating element having an angled transitional neck
CA2961767C (en) 2009-06-23 2018-08-14 Endospan Ltd. Vascular prostheses for treating aneurysms
US20110004294A1 (en) * 2009-07-02 2011-01-06 Abbott Laboratories Fatigue-resistant stent
US8357178B2 (en) * 2009-07-08 2013-01-22 Concentric Medical, Inc. Vascular and bodily duct treatment devices and methods
US8529596B2 (en) 2009-07-08 2013-09-10 Concentric Medical, Inc. Vascular and bodily duct treatment devices and methods
US8357179B2 (en) * 2009-07-08 2013-01-22 Concentric Medical, Inc. Vascular and bodily duct treatment devices and methods
US8795345B2 (en) * 2009-07-08 2014-08-05 Concentric Medical, Inc. Vascular and bodily duct treatment devices and methods
US20110009941A1 (en) * 2009-07-08 2011-01-13 Concentric Medical, Inc. Vascular and bodily duct treatment devices and methods
US8795317B2 (en) * 2009-07-08 2014-08-05 Concentric Medical, Inc. Embolic obstruction retrieval devices and methods
US8979892B2 (en) 2009-07-09 2015-03-17 Endospan Ltd. Apparatus for closure of a lumen and methods of using the same
WO2011008989A2 (en) 2009-07-15 2011-01-20 Endologix, Inc. Stent graft
ES2549000T3 (en) 2009-07-27 2015-10-22 Endologix, Inc. Endoprosthesis
DE202009010388U1 (en) * 2009-07-31 2010-12-09 Düring, Klaus, Dr. Fixation device for fixing an apnea stent in the airway
US8114149B2 (en) * 2009-10-20 2012-02-14 Svelte Medical Systems, Inc. Hybrid stent with helical connectors
US9358140B1 (en) 2009-11-18 2016-06-07 Aneuclose Llc Stent with outer member to embolize an aneurysm
US8945203B2 (en) 2009-11-30 2015-02-03 Endospan Ltd. Multi-component stent-graft system for implantation in a blood vessel with multiple branches
US9101457B2 (en) 2009-12-08 2015-08-11 Endospan Ltd. Endovascular stent-graft system with fenestrated and crossing stent-grafts
US20110144577A1 (en) * 2009-12-11 2011-06-16 John Stankus Hydrophilic coatings with tunable composition for drug coated balloon
US8951595B2 (en) * 2009-12-11 2015-02-10 Abbott Cardiovascular Systems Inc. Coatings with tunable molecular architecture for drug-coated balloon
US8480620B2 (en) * 2009-12-11 2013-07-09 Abbott Cardiovascular Systems Inc. Coatings with tunable solubility profile for drug-coated balloon
GB2476479B (en) 2009-12-22 2012-06-20 Cook Medical Technologies Llc Implantable device
US20110276078A1 (en) 2009-12-30 2011-11-10 Nellix, Inc. Filling structure for a graft system and methods of use
EP2533722B1 (en) 2010-02-08 2017-03-29 Endospan Ltd. Thermal energy application for prevention and management of endoleaks in stent-grafts
US20110208289A1 (en) * 2010-02-25 2011-08-25 Endospan Ltd. Flexible Stent-Grafts
US9199066B2 (en) 2010-03-12 2015-12-01 Quattro Vascular Pte Ltd. Device and method for compartmental vessel treatment
WO2011119536A1 (en) 2010-03-22 2011-09-29 Abbott Cardiovascular Systems Inc. Stent delivery system having a fibrous matrix covering with improved stent retention
EP2380604A1 (en) 2010-04-19 2011-10-26 InnoRa Gmbh Improved coating formulations for scoring or cutting balloon catheters
US9241755B2 (en) 2010-05-11 2016-01-26 Alcon Research, Ltd. Capsule polishing device and method for capsule polishing
US8535380B2 (en) 2010-05-13 2013-09-17 Stout Medical Group, L.P. Fixation device and method
US8389041B2 (en) 2010-06-17 2013-03-05 Abbott Cardiovascular Systems, Inc. Systems and methods for rotating and coating an implantable device
AU2011285808B2 (en) 2010-08-02 2015-04-30 Cardinal Health 529, Llc Flexible helical stent having intermediated non-helical region
EP2600801B1 (en) 2010-08-02 2017-07-19 Cordis Corporation Flexible helical stent having intermediate structural feature
KR20160103151A (en) 2010-08-02 2016-08-31 코디스 코포레이션 Flexible helical stent having different helical regions
EP2600805B1 (en) 2010-08-02 2021-10-06 Cardinal Health 529, LLC Flexible stent having protruding hinges
WO2012027490A2 (en) 2010-08-24 2012-03-01 Stout Medical Group, L.P. Support device and method for use
US8632559B2 (en) 2010-09-21 2014-01-21 Angioscore, Inc. Method and system for treating valve stenosis
US9149388B2 (en) 2010-09-29 2015-10-06 Alcon Research, Ltd. Attenuated RF power for automated capsulorhexis
EP2629684B1 (en) 2010-10-22 2018-07-25 Neuravi Limited Clot engagement and removal system
US20120109279A1 (en) 2010-11-02 2012-05-03 Endologix, Inc. Apparatus and method of placement of a graft or graft system
US9149286B1 (en) 2010-11-12 2015-10-06 Flexmedex, LLC Guidance tool and method for use
WO2012068298A1 (en) 2010-11-17 2012-05-24 Endologix, Inc. Devices and methods to treat vascular dissections
JP6010545B2 (en) 2010-12-23 2016-10-19 トゥエルヴ, インコーポレイテッド System for mitral valve repair and replacement
US8512395B2 (en) 2010-12-30 2013-08-20 Boston Scientific Scimed, Inc. Stent with horseshoe shaped bridges
US8801768B2 (en) 2011-01-21 2014-08-12 Endologix, Inc. Graft systems having semi-permeable filling structures and methods for their use
US9526638B2 (en) 2011-02-03 2016-12-27 Endospan Ltd. Implantable medical devices constructed of shape memory material
CA2826615A1 (en) * 2011-02-04 2012-08-09 Concentric Medical, Inc. Vascular and bodily duct treatment devices and methods
WO2012111006A1 (en) 2011-02-17 2012-08-23 Endospan Ltd. Vascular bands and delivery systems therefor
EP2680915B1 (en) 2011-03-01 2021-12-22 Endologix LLC Catheter system
WO2012117395A1 (en) 2011-03-02 2012-09-07 Endospan Ltd. Reduced-strain extra- vascular ring for treating aortic aneurysm
JP2014511247A (en) 2011-03-03 2014-05-15 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 Low strain high strength stent
US8790388B2 (en) 2011-03-03 2014-07-29 Boston Scientific Scimed, Inc. Stent with reduced profile
US12076037B2 (en) 2011-03-09 2024-09-03 Neuravi Limited Systems and methods to restore perfusion to a vessel
US11259824B2 (en) 2011-03-09 2022-03-01 Neuravi Limited Clot retrieval device for removing occlusive clot from a blood vessel
WO2012120490A2 (en) 2011-03-09 2012-09-13 Neuravi Limited A clot retrieval device for removing occlusive clot from a blood vessel
EP2685934A4 (en) * 2011-03-17 2015-01-07 Pq Bypass Inc Differential dilation stent and method of use
ES2566105T3 (en) * 2011-04-04 2016-04-11 Allium Medical Solutions Ltd. System and method of manufacturing a stent
JP5976777B2 (en) 2011-04-06 2016-08-24 エンドーロジックス インコーポレイテッド Methods and systems for the treatment of intravascular aneurysms
US9101507B2 (en) 2011-05-18 2015-08-11 Ralph F. Caselnova Apparatus and method for proximal-to-distal endoluminal stent deployment
WO2012158881A1 (en) * 2011-05-19 2012-11-22 Tyco Healthcare Group Lp Vascular remodeling device
US10092426B2 (en) * 2011-05-31 2018-10-09 Cook Medical Technologies Llc Non-foreshortening, axial tension constrainable stent
US10285798B2 (en) 2011-06-03 2019-05-14 Merit Medical Systems, Inc. Esophageal stent
US8574287B2 (en) 2011-06-14 2013-11-05 Endospan Ltd. Stents incorporating a plurality of strain-distribution locations
EP2579811B1 (en) 2011-06-21 2016-03-16 Endospan Ltd Endovascular system with circumferentially-overlapping stent-grafts
CA2840084C (en) 2011-06-21 2019-11-05 Foundry Newco Xii, Inc. Prosthetic heart valve devices and associated systems and methods
US9254209B2 (en) 2011-07-07 2016-02-09 Endospan Ltd. Stent fixation with reduced plastic deformation
CN103930058A (en) 2011-08-23 2014-07-16 弗雷科斯米德克斯有限公司 Tissue removal device and method
WO2013030818A2 (en) 2011-08-28 2013-03-07 Endospan Ltd. Stent-grafts with post-deployment variable axial and radial displacement
US9655722B2 (en) 2011-10-19 2017-05-23 Twelve, Inc. Prosthetic heart valve devices, prosthetic mitral valves and associated systems and methods
CN107028685B (en) 2011-10-19 2019-11-15 托尔福公司 Artificial heart valve film device, artificial mitral valve and related systems and methods
US11202704B2 (en) 2011-10-19 2021-12-21 Twelve, Inc. Prosthetic heart valve devices, prosthetic mitral valves and associated systems and methods
US9763780B2 (en) 2011-10-19 2017-09-19 Twelve, Inc. Devices, systems and methods for heart valve replacement
WO2013059743A1 (en) 2011-10-19 2013-04-25 Foundry Newco Xii, Inc. Devices, systems and methods for heart valve replacement
US9039757B2 (en) 2011-10-19 2015-05-26 Twelve, Inc. Prosthetic heart valve devices, prosthetic mitral valves and associated systems and methods
WO2013065040A1 (en) 2011-10-30 2013-05-10 Endospan Ltd. Triple-collar stent-graft
US8986368B2 (en) * 2011-10-31 2015-03-24 Merit Medical Systems, Inc. Esophageal stent with valve
EP2785277B1 (en) 2011-12-04 2017-04-05 Endospan Ltd. Branched stent-graft system
CN104159541A (en) 2012-02-01 2014-11-19 夸超脉管私人有限公司 Device for compartmental dilatation of blood vessels
EP3542849B1 (en) 2012-02-08 2020-12-09 TriReme Medical, LLC Constraining structure with non-linear axial struts
US9216033B2 (en) 2012-02-08 2015-12-22 Quattro Vascular Pte Ltd. System and method for treating biological vessels
US9579198B2 (en) 2012-03-01 2017-02-28 Twelve, Inc. Hydraulic delivery systems for prosthetic heart valve devices and associated methods
US8992595B2 (en) 2012-04-04 2015-03-31 Trivascular, Inc. Durable stent graft with tapered struts and stable delivery methods and devices
US9498363B2 (en) 2012-04-06 2016-11-22 Trivascular, Inc. Delivery catheter for endovascular device
WO2013171730A1 (en) 2012-05-15 2013-11-21 Endospan Ltd. Stent-graft with fixation elements that are radially confined for delivery
KR102313261B1 (en) 2012-06-05 2021-10-14 메리트 메디컬 시스템즈, 인크. Esophageal stent
US8834556B2 (en) * 2012-08-13 2014-09-16 Abbott Cardiovascular Systems Inc. Segmented scaffold designs
US9254203B2 (en) 2012-08-20 2016-02-09 Boston Scientific Scimed, Inc. Delivery device
US9463177B2 (en) 2012-09-10 2016-10-11 The Regents Of The University Of California Compounds and methods for modulating vascular injury
US8784434B2 (en) 2012-11-20 2014-07-22 Inceptus Medical, Inc. Methods and apparatus for treating embolism
DE102012112733A1 (en) * 2012-12-20 2014-06-26 Acandis Gmbh & Co. Kg Medical system e.g. bifurcation stent system installed in blood vessel, has a mesh structure having a partly hollow truncated cone-shaped transition section, in which the distal end portions are formed in hollow cylindrical shape
USD707818S1 (en) 2013-03-05 2014-06-24 Alcon Research Ltd. Capsulorhexis handpiece
RU2658453C2 (en) 2013-03-05 2018-06-21 Мерит Медикал Системз, Инк. Reinforced valve
US9668892B2 (en) 2013-03-11 2017-06-06 Endospan Ltd. Multi-component stent-graft system for aortic dissections
CN105517509B (en) 2013-03-13 2017-08-08 爱德华兹生命科学卡迪尔克有限责任公司 Radial type joint valve bracket and method
US9642635B2 (en) 2013-03-13 2017-05-09 Neuravi Limited Clot removal device
ES2960917T3 (en) 2013-03-14 2024-03-07 Neuravi Ltd Clot retrieval device to remove occlusive clots from a blood vessel
US9433429B2 (en) 2013-03-14 2016-09-06 Neuravi Limited Clot retrieval devices
US10201638B2 (en) 2013-03-14 2019-02-12 Endologix, Inc. Systems and methods for forming materials in situ within a medical device
US10201360B2 (en) 2013-03-14 2019-02-12 Neuravi Limited Devices and methods for removal of acute blockages from blood vessels
US9545301B2 (en) 2013-03-15 2017-01-17 Covidien Lp Coated medical devices and methods of making and using same
US9320592B2 (en) 2013-03-15 2016-04-26 Covidien Lp Coated medical devices and methods of making and using same
EP2967927A4 (en) 2013-03-15 2016-10-12 Merit Medical Systems Inc Esophageal stent
US9907684B2 (en) 2013-05-08 2018-03-06 Aneuclose Llc Method of radially-asymmetric stent expansion
EP2999435B1 (en) 2013-05-20 2022-12-21 Twelve, Inc. Implantable heart valve devices, mitral valve repair devices and associated systems
US9320628B2 (en) * 2013-09-09 2016-04-26 Boston Scientific Scimed, Inc. Endoprosthesis devices including biostable and bioabsorable regions
US10117668B2 (en) 2013-10-08 2018-11-06 The Spectranetics Corporation Balloon catheter with non-deployable stent having improved stability
CN203829102U (en) * 2013-10-09 2014-09-17 唐利龙 Support for preformed guide-wire channel
WO2015061365A1 (en) 2013-10-21 2015-04-30 Inceptus Medical, Llc Methods and apparatus for treating embolism
CN111419472B (en) 2013-11-11 2023-01-10 爱德华兹生命科学卡迪尔克有限责任公司 System and method for manufacturing stent frames
US10603197B2 (en) 2013-11-19 2020-03-31 Endospan Ltd. Stent system with radial-expansion locking
US9668890B2 (en) 2013-11-22 2017-06-06 Covidien Lp Anti-thrombogenic medical devices and methods
CN103720529B (en) * 2013-12-30 2017-02-08 先健科技(深圳)有限公司 Arcus aortae intraoperative stent and method for manufacturing stent
USD737438S1 (en) 2014-03-04 2015-08-25 Novartis Ag Capsulorhexis handpiece
US10285720B2 (en) 2014-03-11 2019-05-14 Neuravi Limited Clot retrieval system for removing occlusive clot from a blood vessel
US10441301B2 (en) 2014-06-13 2019-10-15 Neuravi Limited Devices and methods for removal of acute blockages from blood vessels
US10792056B2 (en) 2014-06-13 2020-10-06 Neuravi Limited Devices and methods for removal of acute blockages from blood vessels
US9545263B2 (en) 2014-06-19 2017-01-17 Limflow Gmbh Devices and methods for treating lower extremity vasculature
US10265086B2 (en) 2014-06-30 2019-04-23 Neuravi Limited System for removing a clot from a blood vessel
CN107106822B (en) 2014-11-17 2021-05-04 特里雷米医疗有限责任公司 Balloon catheter system
US11253278B2 (en) 2014-11-26 2022-02-22 Neuravi Limited Clot retrieval system for removing occlusive clot from a blood vessel
CN106999196B (en) 2014-11-26 2020-07-28 尼尔拉维有限公司 Thrombus retrieval device for removing obstructive thrombus from blood vessel
US10617435B2 (en) 2014-11-26 2020-04-14 Neuravi Limited Clot retrieval device for removing clot from a blood vessel
US9789228B2 (en) 2014-12-11 2017-10-17 Covidien Lp Antimicrobial coatings for medical devices and processes for preparing such coatings
CN106029005B (en) 2014-12-18 2018-01-19 恩都思潘有限公司 The Endovascular stent-graft of horizontal conduit with tired resistance
EP3139860B1 (en) 2015-06-30 2024-06-12 Endologix LLC Locking assembly for coupling guidewire to delivery system
JP6543119B2 (en) * 2015-07-10 2019-07-10 有限会社Ptmc研究所 Stent graft
US10327924B2 (en) * 2015-07-19 2019-06-25 Sanford Health Bridging stent graft with combination balloon expandable and self-expandable stents and methods for use
CN111658234B (en) 2015-08-21 2023-03-10 托尔福公司 Implantable heart valve devices, mitral valve repair devices, and associated systems and methods
US10441447B2 (en) 2015-09-11 2019-10-15 Cook Medical Technologies Llc Variable radial stiffness and variable diameter intraluminal device
EP4233744A3 (en) 2015-10-23 2023-11-01 Inari Medical, Inc. Device for intravascular treatment of vascular occlusion
CN105769383B (en) * 2016-03-18 2019-12-10 杭州唯强医疗科技有限公司 Aorta bare stent and aorta interlayer stent
CN109069272A (en) 2016-04-29 2018-12-21 美敦力瓦斯科尔勒公司 Prosthetic heart valve equipment and associated system and method with the anchor log with tether
JP7086935B2 (en) 2016-08-17 2022-06-20 ニューラヴィ・リミテッド Thrombus recovery system for removing thromboangiitis obliterans from blood vessels
JP7046924B2 (en) 2016-09-06 2022-04-04 ニューラヴィ・リミテッド Clot recovery device for removing obstructive clots from blood vessels
FI3528717T3 (en) 2016-10-24 2024-08-09 Inari Medical Inc Devices for treating vascular occlusion
US10449069B2 (en) 2016-11-14 2019-10-22 Covidien Lp Stent
US10905572B2 (en) * 2016-11-14 2021-02-02 Covidien Lp Stent
US10258488B2 (en) * 2016-11-14 2019-04-16 Covidien Lp Stent
CN110730634A (en) 2017-04-10 2020-01-24 林弗洛公司 Apparatus and method for treating the vasculature of a lower limb
US10433961B2 (en) 2017-04-18 2019-10-08 Twelve, Inc. Delivery systems with tethers for prosthetic heart valve devices and associated methods
US10575950B2 (en) 2017-04-18 2020-03-03 Twelve, Inc. Hydraulic systems for delivering prosthetic heart valve devices and associated methods
US10702378B2 (en) 2017-04-18 2020-07-07 Twelve, Inc. Prosthetic heart valve device and associated systems and methods
US10792151B2 (en) 2017-05-11 2020-10-06 Twelve, Inc. Delivery systems for delivering prosthetic heart valve devices and associated methods
US10646338B2 (en) 2017-06-02 2020-05-12 Twelve, Inc. Delivery systems with telescoping capsules for deploying prosthetic heart valve devices and associated methods
US10709591B2 (en) 2017-06-06 2020-07-14 Twelve, Inc. Crimping device and method for loading stents and prosthetic heart valves
US10786352B2 (en) 2017-07-06 2020-09-29 Twelve, Inc. Prosthetic heart valve devices and associated systems and methods
US10729541B2 (en) 2017-07-06 2020-08-04 Twelve, Inc. Prosthetic heart valve devices and associated systems and methods
US10238513B2 (en) 2017-07-19 2019-03-26 Abbott Cardiovascular Systems Inc. Intravascular stent
CA3074564A1 (en) 2017-09-06 2019-03-14 Inari Medical, Inc. Hemostasis valves and methods of use
US11154314B2 (en) 2018-01-26 2021-10-26 Inari Medical, Inc. Single insertion delivery system for treating embolism and associated systems and methods
AU2019321256B2 (en) 2018-08-13 2023-06-22 Inari Medical, Inc. System for treating embolism and associated devices and methods
US10842498B2 (en) 2018-09-13 2020-11-24 Neuravi Limited Systems and methods of restoring perfusion to a vessel
US11406416B2 (en) 2018-10-02 2022-08-09 Neuravi Limited Joint assembly for vasculature obstruction capture device
JP7466531B2 (en) 2018-10-09 2024-04-12 リムフロウ・ゲゼルシャフト・ミット・ベシュレンクテル・ハフツング Catheter positioning device and method
ES2910600T3 (en) 2019-03-04 2022-05-12 Neuravi Ltd Powered Clot Recovery Catheter
CA3133857A1 (en) 2019-03-20 2020-09-24 inQB8 Medical Technologies, LLC Aortic dissection implant
US11517457B2 (en) 2019-07-03 2022-12-06 Abbott Cardiovascular Systems Inc. Intravascular stent
EP4427686A2 (en) 2019-09-11 2024-09-11 Neuravi Limited Expandable mouth catheter
AU2020368528A1 (en) 2019-10-16 2022-04-21 Inari Medical, Inc. Systems, devices, and methods for treating vascular occlusions
US11712231B2 (en) 2019-10-29 2023-08-01 Neuravi Limited Proximal locking assembly design for dual stent mechanical thrombectomy device
CN114929163A (en) 2019-11-01 2022-08-19 林弗洛公司 Device and method for increasing blood perfusion to distal extremities
US11779364B2 (en) 2019-11-27 2023-10-10 Neuravi Limited Actuated expandable mouth thrombectomy catheter
US11839725B2 (en) 2019-11-27 2023-12-12 Neuravi Limited Clot retrieval device with outer sheath and inner catheter
US11517340B2 (en) 2019-12-03 2022-12-06 Neuravi Limited Stentriever devices for removing an occlusive clot from a vessel and methods thereof
US11633198B2 (en) 2020-03-05 2023-04-25 Neuravi Limited Catheter proximal joint
US11944327B2 (en) 2020-03-05 2024-04-02 Neuravi Limited Expandable mouth aspirating clot retrieval catheter
US11883043B2 (en) 2020-03-31 2024-01-30 DePuy Synthes Products, Inc. Catheter funnel extension
US11759217B2 (en) 2020-04-07 2023-09-19 Neuravi Limited Catheter tubular support
US11717308B2 (en) 2020-04-17 2023-08-08 Neuravi Limited Clot retrieval device for removing heterogeneous clots from a blood vessel
US11730501B2 (en) 2020-04-17 2023-08-22 Neuravi Limited Floating clot retrieval device for removing clots from a blood vessel
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Citations (85)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3868956A (en) * 1972-06-05 1975-03-04 Ralph J Alfidi Vessel implantable appliance and method of implanting it
US4372600A (en) * 1980-04-07 1983-02-08 The Mead Corporation Bottle carrier
US4390599A (en) * 1980-07-31 1983-06-28 Raychem Corporation Enhanced recovery memory metal device
US4441215A (en) * 1980-11-17 1984-04-10 Kaster Robert L Vascular graft
US4512338A (en) * 1983-01-25 1985-04-23 Balko Alexander B Process for restoring patency to body vessels
US4580568A (en) * 1984-10-01 1986-04-08 Cook, Incorporated Percutaneous endovascular stent and method for insertion thereof
US4649922A (en) * 1986-01-23 1987-03-17 Wiktor Donimik M Catheter arrangement having a variable diameter tip and spring prosthesis
US4655771A (en) * 1982-04-30 1987-04-07 Shepherd Patents S.A. Prosthesis comprising an expansible or contractile tubular body
US4681110A (en) * 1985-12-02 1987-07-21 Wiktor Dominik M Catheter arrangement having a blood vessel liner, and method of using it
US4732152A (en) * 1984-12-05 1988-03-22 Medinvent S.A. Device for implantation and a method of implantation in a vessel using such device
US4733665A (en) * 1985-11-07 1988-03-29 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
US4795458A (en) * 1987-07-02 1989-01-03 Regan Barrie F Stent for use following balloon angioplasty
US4830003A (en) * 1988-06-17 1989-05-16 Wolff Rodney G Compressive stent and delivery system
US4878906A (en) * 1986-03-25 1989-11-07 Servetus Partnership Endoprosthesis for repairing a damaged vessel
US4886062A (en) * 1987-10-19 1989-12-12 Medtronic, Inc. Intravascular radially expandable stent and method of implant
US4913141A (en) * 1988-10-25 1990-04-03 Cordis Corporation Apparatus and method for placement of a stent within a subject vessel
US5064435A (en) * 1990-06-28 1991-11-12 Schneider (Usa) Inc. Self-expanding prosthesis having stable axial length
US5102417A (en) * 1985-11-07 1992-04-07 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
US5104404A (en) * 1989-10-02 1992-04-14 Medtronic, Inc. Articulated stent
US5147370A (en) * 1991-06-12 1992-09-15 Mcnamara Thomas O Nitinol stent for hollow body conduits
US5180868A (en) * 1988-06-20 1993-01-19 Battelle Memorial Institute Method of upgrading oils containing hydroxyaromatic hydrocarbon compounds to highly aromatic gasoline
US5192297A (en) * 1991-12-31 1993-03-09 Medtronic, Inc. Apparatus and method for placement and implantation of a stent
US5201757A (en) * 1992-04-03 1993-04-13 Schneider (Usa) Inc. Medial region deployment of radially self-expanding stents
US5226909A (en) * 1989-09-12 1993-07-13 Devices For Vascular Intervention, Inc. Atherectomy device having helical blade and blade guide
US5234457A (en) * 1991-10-09 1993-08-10 Boston Scientific Corporation Impregnated stent
US5282827A (en) * 1991-11-08 1994-02-01 Kensey Nash Corporation Hemostatic puncture closure system and method of use
US5282824A (en) * 1990-10-09 1994-02-01 Cook, Incorporated Percutaneous stent assembly
US5330500A (en) * 1990-10-18 1994-07-19 Song Ho Y Self-expanding endovascular stent with silicone coating
US5354308A (en) * 1992-05-01 1994-10-11 Beth Israel Hospital Association Metal wire stent
US5354309A (en) * 1991-10-11 1994-10-11 Angiomed Ag Apparatus for widening a stenosis in a body cavity
US5356423A (en) * 1991-01-04 1994-10-18 American Medical Systems, Inc. Resectable self-expanding stent
US5383892A (en) * 1991-11-08 1995-01-24 Meadox France Stent for transluminal implantation
US5405377A (en) * 1992-02-21 1995-04-11 Endotech Ltd. Intraluminal stent
US5414664A (en) * 1993-05-28 1995-05-09 Macronix International Co., Ltd. Flash EPROM with block erase flags for over-erase protection
US5441515A (en) * 1993-04-23 1995-08-15 Advanced Cardiovascular Systems, Inc. Ratcheting stent
US5446646A (en) * 1991-03-15 1995-08-29 Kabushiki Kaisha Toshiba Method and apparatus for control of pulse width modulation (PWM) converter
US5445646A (en) * 1993-10-22 1995-08-29 Scimed Lifesystems, Inc. Single layer hydraulic sheath stent delivery apparatus and method
US5449373A (en) * 1994-03-17 1995-09-12 Medinol Ltd. Articulated stent
US5476508A (en) * 1994-05-26 1995-12-19 Tfx Medical Stent with mutually interlocking filaments
US5507771A (en) * 1992-06-15 1996-04-16 Cook Incorporated Stent assembly
US5507767A (en) * 1992-01-15 1996-04-16 Cook Incorporated Spiral stent
US5540712A (en) * 1992-05-01 1996-07-30 Nitinol Medical Technologies, Inc. Stent and method and apparatus for forming and delivering the same
US5545211A (en) * 1993-09-27 1996-08-13 Sooho Medi-Tech Co., Ltd. Stent for expanding a lumen
US5562697A (en) * 1995-09-18 1996-10-08 William Cook, Europe A/S Self-expanding stent assembly and methods for the manufacture thereof
US5562725A (en) * 1992-09-14 1996-10-08 Meadox Medicals Inc. Radially self-expanding implantable intraluminal device
US5591195A (en) * 1995-10-30 1997-01-07 Taheri; Syde Apparatus and method for engrafting a blood vessel
US5601593A (en) * 1995-03-06 1997-02-11 Willy Rusch Ag Stent for placement in a body tube
US5607442A (en) * 1995-11-13 1997-03-04 Isostent, Inc. Stent with improved radiopacity and appearance characteristics
US5643312A (en) * 1994-02-25 1997-07-01 Fischell Robert Stent having a multiplicity of closed circular structures
US5693086A (en) * 1994-02-09 1997-12-02 Boston Scientific Technology, Inc. Apparatus for delivering an endoluminal stent or prosthesis
US5716393A (en) * 1994-05-26 1998-02-10 Angiomed Gmbh & Co. Medizintechnik Kg Stent with an end of greater diameter than its main body
US5733303A (en) * 1994-03-17 1998-03-31 Medinol Ltd. Flexible expandable stent
US5741327A (en) * 1997-05-06 1998-04-21 Global Therapeutics, Inc. Surgical stent featuring radiopaque markers
US5776161A (en) * 1995-10-16 1998-07-07 Instent, Inc. Medical stents, apparatus and method for making same
US5807404A (en) * 1996-09-19 1998-09-15 Medinol Ltd. Stent with variable features to optimize support and method of making such stent
US5810872A (en) * 1997-03-14 1998-09-22 Kanesaka; Nozomu Flexible stent
US5824045A (en) * 1996-10-21 1998-10-20 Inflow Dynamics Inc. Vascular and endoluminal stents
US5824059A (en) * 1997-08-05 1998-10-20 Wijay; Bandula Flexible stent
US5827321A (en) * 1997-02-07 1998-10-27 Cornerstone Devices, Inc. Non-Foreshortening intraluminal prosthesis
US5843244A (en) * 1996-06-13 1998-12-01 Nitinol Devices And Components Shape memory alloy treatment
US5843117A (en) * 1996-02-14 1998-12-01 Inflow Dynamics Inc. Implantable vascular and endoluminal stents and process of fabricating the same
US5853419A (en) * 1997-03-17 1998-12-29 Surface Genesis, Inc. Stent
US5860999A (en) * 1993-02-04 1999-01-19 Angiomed Gmbh & Co.Medizintechnik Kg Stent and method of using same
US5868781A (en) * 1996-10-22 1999-02-09 Scimed Life Systems, Inc. Locking stent
US5868780A (en) * 1996-03-22 1999-02-09 Lashinski; Robert D. Stents for supporting lumens in living tissue
US5879370A (en) * 1994-02-25 1999-03-09 Fischell; Robert E. Stent having a multiplicity of undulating longitudinals
US5895406A (en) * 1996-01-26 1999-04-20 Cordis Corporation Axially flexible stent
US5913895A (en) * 1997-06-02 1999-06-22 Isostent, Inc. Intravascular stent with enhanced rigidity strut members
US5922021A (en) * 1996-04-26 1999-07-13 Jang; G. David Intravascular stent
US5938697A (en) * 1998-03-04 1999-08-17 Scimed Life Systems, Inc. Stent having variable properties
US5954743A (en) * 1996-04-26 1999-09-21 Jang; G. David Intravascular stent
US5955600A (en) * 1996-12-27 1999-09-21 Isis Pharmaceuticals, Inc. Method for the synthesis of nucleotide or oligonucleotide phosphoramidites
US5972018A (en) * 1994-03-17 1999-10-26 Medinol Ltd. Flexible expandable stent
US6010530A (en) * 1995-06-07 2000-01-04 Boston Scientific Technology, Inc. Self-expanding endoluminal prosthesis
US6027526A (en) * 1996-04-10 2000-02-22 Advanced Cardiovascular Systems, Inc. Stent having varied amounts of structural strength along its length
US6056776A (en) * 1991-10-28 2000-05-02 Advanced Cardiovascular System, Inc. Expandable stents and method for making same
US6299635B1 (en) * 1997-09-29 2001-10-09 Cook Incorporated Radially expandable non-axially contracting surgical stent
US6312460B2 (en) * 1999-05-03 2001-11-06 William J. Drasler Intravascular hinge stent
US6348065B1 (en) * 1995-03-01 2002-02-19 Scimed Life Systems, Inc. Longitudinally flexible expandable stent
US6398806B1 (en) * 2000-12-26 2002-06-04 Scimed Life Systems, Inc. Monolayer modification to gold coated stents to reduce adsorption of protein
US6423084B1 (en) * 1997-05-22 2002-07-23 Scimed Life Systems, Inc Variable expansion force stent
US6443982B1 (en) * 1994-03-17 2002-09-03 Medinol, Ltd. Flexible expandable stent
US6451052B1 (en) * 1994-05-19 2002-09-17 Scimed Life Systems, Inc. Tissue supporting devices
US6551350B1 (en) * 1996-12-23 2003-04-22 Gore Enterprise Holdings, Inc. Kink resistant bifurcated prosthesis
US6852124B2 (en) * 1999-04-22 2005-02-08 Advanced Cardiovascular Systems, Inc. Variable strength stent

Family Cites Families (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5384A (en) * 1847-12-04 Improvement in decomposing potash-feldspar for obtaining certain salts
CH678393A5 (en) * 1989-01-26 1991-09-13 Ulrich Prof Dr Med Sigwart
US5372600A (en) * 1991-10-31 1994-12-13 Instent Inc. Stent delivery systems
FR2688401B1 (en) * 1992-03-12 1998-02-27 Thierry Richard EXPANDABLE STENT FOR HUMAN OR ANIMAL TUBULAR MEMBER, AND IMPLEMENTATION TOOL.
WO1994021196A2 (en) * 1993-03-18 1994-09-29 C.R. Bard, Inc. Endovascular stents
US5913897A (en) * 1993-09-16 1999-06-22 Cordis Corporation Endoprosthesis having multiple bridging junctions and procedure
GB2281865B (en) * 1993-09-16 1997-07-30 Cordis Corp Endoprosthesis having multiple laser welded junctions,method and procedure
US5415664A (en) * 1994-03-30 1995-05-16 Corvita Corporation Method and apparatus for introducing a stent or a stent-graft
CA2502504A1 (en) * 1994-05-19 1995-11-30 Scimed Life Systems, Inc. Improved tissue supporting devices
US5817152A (en) * 1994-10-19 1998-10-06 Birdsall; Matthew Connected stent apparatus
US5575818A (en) * 1995-02-14 1996-11-19 Corvita Corporation Endovascular stent with locking ring
US5591197A (en) * 1995-03-14 1997-01-07 Advanced Cardiovascular Systems, Inc. Expandable stent forming projecting barbs and method for deploying
EP0740928B1 (en) * 1995-04-12 2004-07-07 Corvita Europe Self-expanding stent for introducing a medical device in a body cavity and manufacturing process
DK0828461T3 (en) 1995-04-26 2003-05-05 Medinol Ltd Articulated stent with joints that have kink
US5810868A (en) 1995-12-07 1998-09-22 Arterial Vascular Engineering, Inc. Stent for improved transluminal deployment
WO1997025937A1 (en) * 1996-01-18 1997-07-24 Jang G David Programmable variably flexible modular stents
CA2192520A1 (en) * 1996-03-05 1997-09-05 Ian M. Penn Expandable stent and method for delivery of same
DE19617823A1 (en) 1996-05-03 1997-11-13 Sitomed Medizintechnik Vertrie Vascular prosthesis for coronary use
DE69735711T3 (en) * 1996-11-07 2010-07-01 Medtronic Instent Inc., Eden Prairie Stent with variable flexibility
FR2758253B1 (en) * 1997-01-10 1999-04-02 Nycomed Lab Sa IMPLANTABLE DEVICE FOR THE TREATMENT OF A BODY DUCT
US5925061A (en) * 1997-01-13 1999-07-20 Gore Enterprise Holdings, Inc. Low profile vascular stent
US5855600A (en) 1997-08-01 1999-01-05 Inflow Dynamics Inc. Flexible implantable stent with composite design
US20010047200A1 (en) * 1999-10-13 2001-11-29 Raymond Sun Non-foreshortening intraluminal prosthesis

Patent Citations (98)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3868956A (en) * 1972-06-05 1975-03-04 Ralph J Alfidi Vessel implantable appliance and method of implanting it
US4372600A (en) * 1980-04-07 1983-02-08 The Mead Corporation Bottle carrier
US4390599A (en) * 1980-07-31 1983-06-28 Raychem Corporation Enhanced recovery memory metal device
US4441215A (en) * 1980-11-17 1984-04-10 Kaster Robert L Vascular graft
US4655771A (en) * 1982-04-30 1987-04-07 Shepherd Patents S.A. Prosthesis comprising an expansible or contractile tubular body
US4655771B1 (en) * 1982-04-30 1996-09-10 Medinvent Ams Sa Prosthesis comprising an expansible or contractile tubular body
US4512338A (en) * 1983-01-25 1985-04-23 Balko Alexander B Process for restoring patency to body vessels
US4580568A (en) * 1984-10-01 1986-04-08 Cook, Incorporated Percutaneous endovascular stent and method for insertion thereof
US4732152A (en) * 1984-12-05 1988-03-22 Medinvent S.A. Device for implantation and a method of implantation in a vessel using such device
US4733665A (en) * 1985-11-07 1988-03-29 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
US4733665B1 (en) * 1985-11-07 1994-01-11 Expandable Grafts Partnership Expandable intraluminal graft,and method and apparatus for implanting an expandable intraluminal graft
US4733665C2 (en) * 1985-11-07 2002-01-29 Expandable Grafts Partnership Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft
US5102417A (en) * 1985-11-07 1992-04-07 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
US4681110A (en) * 1985-12-02 1987-07-21 Wiktor Dominik M Catheter arrangement having a blood vessel liner, and method of using it
US4649922A (en) * 1986-01-23 1987-03-17 Wiktor Donimik M Catheter arrangement having a variable diameter tip and spring prosthesis
US4878906A (en) * 1986-03-25 1989-11-07 Servetus Partnership Endoprosthesis for repairing a damaged vessel
US4795458A (en) * 1987-07-02 1989-01-03 Regan Barrie F Stent for use following balloon angioplasty
US4886062A (en) * 1987-10-19 1989-12-12 Medtronic, Inc. Intravascular radially expandable stent and method of implant
US4830003A (en) * 1988-06-17 1989-05-16 Wolff Rodney G Compressive stent and delivery system
US5180868A (en) * 1988-06-20 1993-01-19 Battelle Memorial Institute Method of upgrading oils containing hydroxyaromatic hydrocarbon compounds to highly aromatic gasoline
US4913141A (en) * 1988-10-25 1990-04-03 Cordis Corporation Apparatus and method for placement of a stent within a subject vessel
US5226909A (en) * 1989-09-12 1993-07-13 Devices For Vascular Intervention, Inc. Atherectomy device having helical blade and blade guide
US5104404A (en) * 1989-10-02 1992-04-14 Medtronic, Inc. Articulated stent
US5064435A (en) * 1990-06-28 1991-11-12 Schneider (Usa) Inc. Self-expanding prosthesis having stable axial length
US5282824A (en) * 1990-10-09 1994-02-01 Cook, Incorporated Percutaneous stent assembly
US5330500A (en) * 1990-10-18 1994-07-19 Song Ho Y Self-expanding endovascular stent with silicone coating
US5356423A (en) * 1991-01-04 1994-10-18 American Medical Systems, Inc. Resectable self-expanding stent
US5446646A (en) * 1991-03-15 1995-08-29 Kabushiki Kaisha Toshiba Method and apparatus for control of pulse width modulation (PWM) converter
US5147370A (en) * 1991-06-12 1992-09-15 Mcnamara Thomas O Nitinol stent for hollow body conduits
US5234457A (en) * 1991-10-09 1993-08-10 Boston Scientific Corporation Impregnated stent
US5354309A (en) * 1991-10-11 1994-10-11 Angiomed Ag Apparatus for widening a stenosis in a body cavity
US6066167A (en) * 1991-10-28 2000-05-23 Advanced Cardiovascular Systems, Inc. Expandable stents
US6056776A (en) * 1991-10-28 2000-05-02 Advanced Cardiovascular System, Inc. Expandable stents and method for making same
US6432133B1 (en) * 1991-10-28 2002-08-13 Advanced Cardiovascular Systems, Inc. Expandable stents and method for making same
US5383892A (en) * 1991-11-08 1995-01-24 Meadox France Stent for transluminal implantation
US5282827A (en) * 1991-11-08 1994-02-01 Kensey Nash Corporation Hemostatic puncture closure system and method of use
US5192297A (en) * 1991-12-31 1993-03-09 Medtronic, Inc. Apparatus and method for placement and implantation of a stent
US5507767A (en) * 1992-01-15 1996-04-16 Cook Incorporated Spiral stent
US5405377A (en) * 1992-02-21 1995-04-11 Endotech Ltd. Intraluminal stent
US5201757A (en) * 1992-04-03 1993-04-13 Schneider (Usa) Inc. Medial region deployment of radially self-expanding stents
US5354308A (en) * 1992-05-01 1994-10-11 Beth Israel Hospital Association Metal wire stent
US5540712A (en) * 1992-05-01 1996-07-30 Nitinol Medical Technologies, Inc. Stent and method and apparatus for forming and delivering the same
US5507771A (en) * 1992-06-15 1996-04-16 Cook Incorporated Stent assembly
US5562725A (en) * 1992-09-14 1996-10-08 Meadox Medicals Inc. Radially self-expanding implantable intraluminal device
US5860999A (en) * 1993-02-04 1999-01-19 Angiomed Gmbh & Co.Medizintechnik Kg Stent and method of using same
US5441515A (en) * 1993-04-23 1995-08-15 Advanced Cardiovascular Systems, Inc. Ratcheting stent
US5414664A (en) * 1993-05-28 1995-05-09 Macronix International Co., Ltd. Flash EPROM with block erase flags for over-erase protection
US5545211A (en) * 1993-09-27 1996-08-13 Sooho Medi-Tech Co., Ltd. Stent for expanding a lumen
US5445646A (en) * 1993-10-22 1995-08-29 Scimed Lifesystems, Inc. Single layer hydraulic sheath stent delivery apparatus and method
US5693086A (en) * 1994-02-09 1997-12-02 Boston Scientific Technology, Inc. Apparatus for delivering an endoluminal stent or prosthesis
US5879370A (en) * 1994-02-25 1999-03-09 Fischell; Robert E. Stent having a multiplicity of undulating longitudinals
US5643312A (en) * 1994-02-25 1997-07-01 Fischell Robert Stent having a multiplicity of closed circular structures
US5449373A (en) * 1994-03-17 1995-09-12 Medinol Ltd. Articulated stent
US5733303A (en) * 1994-03-17 1998-03-31 Medinol Ltd. Flexible expandable stent
US6443982B1 (en) * 1994-03-17 2002-09-03 Medinol, Ltd. Flexible expandable stent
US5972018A (en) * 1994-03-17 1999-10-26 Medinol Ltd. Flexible expandable stent
US5980552A (en) * 1994-03-17 1999-11-09 Medinol Ltd. Articulated stent
US6451052B1 (en) * 1994-05-19 2002-09-17 Scimed Life Systems, Inc. Tissue supporting devices
US5476508A (en) * 1994-05-26 1995-12-19 Tfx Medical Stent with mutually interlocking filaments
US6053941A (en) * 1994-05-26 2000-04-25 Angiomed Gmbh & Co. Medizintechnik Kg Stent with an end of greater diameter than its main body
US5716393A (en) * 1994-05-26 1998-02-10 Angiomed Gmbh & Co. Medizintechnik Kg Stent with an end of greater diameter than its main body
US5902317A (en) * 1994-06-01 1999-05-11 Nitinol Medical Technologies, Inc. Stent and method and apparatus for forming and delivering the same
US6348065B1 (en) * 1995-03-01 2002-02-19 Scimed Life Systems, Inc. Longitudinally flexible expandable stent
US5601593A (en) * 1995-03-06 1997-02-11 Willy Rusch Ag Stent for placement in a body tube
US6010530A (en) * 1995-06-07 2000-01-04 Boston Scientific Technology, Inc. Self-expanding endoluminal prosthesis
US5562697A (en) * 1995-09-18 1996-10-08 William Cook, Europe A/S Self-expanding stent assembly and methods for the manufacture thereof
US5776161A (en) * 1995-10-16 1998-07-07 Instent, Inc. Medical stents, apparatus and method for making same
US5591195A (en) * 1995-10-30 1997-01-07 Taheri; Syde Apparatus and method for engrafting a blood vessel
US5607442A (en) * 1995-11-13 1997-03-04 Isostent, Inc. Stent with improved radiopacity and appearance characteristics
US5895406A (en) * 1996-01-26 1999-04-20 Cordis Corporation Axially flexible stent
US5843117A (en) * 1996-02-14 1998-12-01 Inflow Dynamics Inc. Implantable vascular and endoluminal stents and process of fabricating the same
US5868780A (en) * 1996-03-22 1999-02-09 Lashinski; Robert D. Stents for supporting lumens in living tissue
US6027526A (en) * 1996-04-10 2000-02-22 Advanced Cardiovascular Systems, Inc. Stent having varied amounts of structural strength along its length
US5922021A (en) * 1996-04-26 1999-07-13 Jang; G. David Intravascular stent
US5954743A (en) * 1996-04-26 1999-09-21 Jang; G. David Intravascular stent
US20020169500A1 (en) * 1996-04-26 2002-11-14 Jang G. David Intravascular stent
US5843244A (en) * 1996-06-13 1998-12-01 Nitinol Devices And Components Shape memory alloy treatment
US5807404A (en) * 1996-09-19 1998-09-15 Medinol Ltd. Stent with variable features to optimize support and method of making such stent
US5824045A (en) * 1996-10-21 1998-10-20 Inflow Dynamics Inc. Vascular and endoluminal stents
US6022371A (en) * 1996-10-22 2000-02-08 Scimed Life Systems, Inc. Locking stent
US5868781A (en) * 1996-10-22 1999-02-09 Scimed Life Systems, Inc. Locking stent
US6551350B1 (en) * 1996-12-23 2003-04-22 Gore Enterprise Holdings, Inc. Kink resistant bifurcated prosthesis
US5955600A (en) * 1996-12-27 1999-09-21 Isis Pharmaceuticals, Inc. Method for the synthesis of nucleotide or oligonucleotide phosphoramidites
US5827321A (en) * 1997-02-07 1998-10-27 Cornerstone Devices, Inc. Non-Foreshortening intraluminal prosthesis
US6106548A (en) * 1997-02-07 2000-08-22 Endosystems Llc Non-foreshortening intraluminal prosthesis
US6475236B1 (en) * 1997-02-07 2002-11-05 Endosystems, Llc Non-foreshortening intraluminal prosthesis
US6764506B2 (en) * 1997-02-07 2004-07-20 Endosystems Llc Non-foreshortening intraluminal prosthesis
US5810872A (en) * 1997-03-14 1998-09-22 Kanesaka; Nozomu Flexible stent
US5853419A (en) * 1997-03-17 1998-12-29 Surface Genesis, Inc. Stent
US5741327A (en) * 1997-05-06 1998-04-21 Global Therapeutics, Inc. Surgical stent featuring radiopaque markers
US6423084B1 (en) * 1997-05-22 2002-07-23 Scimed Life Systems, Inc Variable expansion force stent
US5913895A (en) * 1997-06-02 1999-06-22 Isostent, Inc. Intravascular stent with enhanced rigidity strut members
US5824059A (en) * 1997-08-05 1998-10-20 Wijay; Bandula Flexible stent
US6299635B1 (en) * 1997-09-29 2001-10-09 Cook Incorporated Radially expandable non-axially contracting surgical stent
US5938697A (en) * 1998-03-04 1999-08-17 Scimed Life Systems, Inc. Stent having variable properties
US6852124B2 (en) * 1999-04-22 2005-02-08 Advanced Cardiovascular Systems, Inc. Variable strength stent
US6312460B2 (en) * 1999-05-03 2001-11-06 William J. Drasler Intravascular hinge stent
US6398806B1 (en) * 2000-12-26 2002-06-04 Scimed Life Systems, Inc. Monolayer modification to gold coated stents to reduce adsorption of protein

Cited By (18)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8998972B2 (en) 2002-09-02 2015-04-07 Anson Medical, Ltd. Flexible stent-graft
US20060149351A1 (en) * 2002-09-02 2006-07-06 Amie Smirthwaite Flexible stent-graft
US12076255B2 (en) 2016-03-31 2024-09-03 Vesper Medical, Inc. Intravascular implants
US11628075B2 (en) 2016-03-31 2023-04-18 Vesper Medical, Inc. Intravascular implants
US11484422B2 (en) 2016-03-31 2022-11-01 Vesper Medical, Inc. Intravascular implants
US10702405B2 (en) 2016-03-31 2020-07-07 Vesper Medical, Inc. Intravascular implants
US10758381B2 (en) 2016-03-31 2020-09-01 Vesper Medical, Inc. Intravascular implants
US10849769B2 (en) 2017-08-23 2020-12-01 Vesper Medical, Inc. Non-foreshortening stent
US10512556B2 (en) 2017-09-08 2019-12-24 Vesper Medical, Inc. Hybrid stent
US11376142B2 (en) 2017-09-08 2022-07-05 Vesper Medical, Inc. Hybrid stent
US10588764B2 (en) 2017-09-08 2020-03-17 Vesper Medical, Inc. Hybrid stent
US11628076B2 (en) 2017-09-08 2023-04-18 Vesper Medical, Inc. Hybrid stent
US10271977B2 (en) 2017-09-08 2019-04-30 Vesper Medical, Inc. Hybrid stent
US11364134B2 (en) 2018-02-15 2022-06-21 Vesper Medical, Inc. Tapering stent
US11344439B2 (en) 2018-03-09 2022-05-31 Vesper Medical, Inc. Implantable stent
US10500078B2 (en) 2018-03-09 2019-12-10 Vesper Medical, Inc. Implantable stent
US11980555B2 (en) 2018-03-09 2024-05-14 Vesper Medical, Inc. Implantable stent
US11357650B2 (en) 2019-02-28 2022-06-14 Vesper Medical, Inc. Hybrid stent

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JP2001511044A (en) 2001-08-07
EP1028772A1 (en) 2000-08-23
US6764506B2 (en) 2004-07-20
US6475236B1 (en) 2002-11-05
US5827321A (en) 1998-10-27
US20030055490A1 (en) 2003-03-20
US20070213808A1 (en) 2007-09-13
EP1028772A4 (en) 2006-07-05
US6106548A (en) 2000-08-22
CA2280131A1 (en) 1998-08-13
US8882823B2 (en) 2014-11-11
WO1998034668A1 (en) 1998-08-13
US20070213807A1 (en) 2007-09-13
CA2280131C (en) 2007-03-20

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