WO2015126768A1 - Ensembles greffon circulaire formés à partir d'un ou plusieurs éléments structuraux sélectionnés de façon avantageuse - Google Patents

Ensembles greffon circulaire formés à partir d'un ou plusieurs éléments structuraux sélectionnés de façon avantageuse Download PDF

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Publication number
WO2015126768A1
WO2015126768A1 PCT/US2015/015959 US2015015959W WO2015126768A1 WO 2015126768 A1 WO2015126768 A1 WO 2015126768A1 US 2015015959 W US2015015959 W US 2015015959W WO 2015126768 A1 WO2015126768 A1 WO 2015126768A1
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WO
WIPO (PCT)
Prior art keywords
main body
stent
frame
graft
prosthetic device
Prior art date
Application number
PCT/US2015/015959
Other languages
English (en)
Inventor
Ali SHAHRIARI
Original Assignee
Aortic Innovations Surena, Llc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Aortic Innovations Surena, Llc filed Critical Aortic Innovations Surena, Llc
Publication of WO2015126768A1 publication Critical patent/WO2015126768A1/fr
Priority to US15/221,724 priority Critical patent/US20160361153A1/en

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06—Blood vessels
    • A61F2/07—Stent-grafts
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/848—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents having means for fixation to the vessel wall, e.g. barbs
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/89—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure the wire-like elements comprising two or more adjacent rings flexibly connected by separate members
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06—Blood vessels
    • A61F2002/061—Blood vessels provided with means for allowing access to secondary lumens
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06—Blood vessels
    • A61F2002/065—Y-shaped blood vessels
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/848—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents having means for fixation to the vessel wall, e.g. barbs
    • A61F2002/8483—Barbs
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/848—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents having means for fixation to the vessel wall, e.g. barbs
    • A61F2002/8486—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents having means for fixation to the vessel wall, e.g. barbs provided on at least one of the ends

Definitions

  • the present disclosure relates to devices that may be used to treat aortic aneurysms.
  • the devices described may also be used for the treatment of thoracoabdominal, arch and ascending aneurysms.
  • Endo vascular technology has revolutionized the treatment of abdominal aortic aneurysms. This technology has shifted the treatment of these deadly disorders from an invasive, morbid operation to a minimally invasive option with low morbidity and mortality and length of stay. Although many patients are candidates for this less invasive repair with conventional devices, a large group of patients are not treatable because of anatomical restrictions. Some of these patients may be candidates for treatment with conventional fenestrated endografts, however there are significant limitations to the use of that technology.
  • stents have sufficient structural rigidity that they do not collapse once implanted within a patient, yet must also have sufficient expansion properties that they can be inflated during operation into an expanded state from the less invasive contracted state they are in during operation. Additionally, the stents must mimic the flexibility of the portion of the artery that they are being inserted in, often times requiring flexible tortuosity in order to maintain proper blood flow and to reduce the risk of compression and kinking.
  • Stents typically are formed by selecting one material that forms each portion of the material used to form the stent frame.
  • the material can be sized according to a desired diameter or shape, but selection of characteristics for use in stent design is limited. In certain instances, having a selected radial or axial strength is desired.
  • a stent assembly includes a first support ring, a second support ring, and a billowing graft.
  • Each support ring may be made of shape memory wire, stainless steel, or other materials.
  • the first support ring has interconnected circumferentially alternating first inner prongs and first outer prongs, the first inner prongs defining a first inner diameter around a central longitudinal axis, and the first outer prongs defining a first outer diameter around the central longitudinal axis greater than the first inner diameter.
  • the second support ring is spaced from the first support ring along the central longitudinal axis.
  • the second support ring has interconnected circumferentially alternating second inner prongs and second outer prongs, the second inner prongs defining a second inner diameter around the central longitudinal axis, and the second outer prongs defining a second outer diameter around the central longitudinal axis greater than the second inner diameter.
  • the billowing graft engages the first support ring and second support ring, the billowing graft following a waving peripheral path at least partially around at least one of the first support ring and second support ring.
  • a circumferential position of a particular first inner prong is aligned with a circumferential position of a particular second inner prong, and circumferential positions of two first outer prongs adjacent the particular first inner prong are aligned respectively with circumferential positions of two second outer prongs adjacent the particular second inner prong such that a longitudinal channel is defined along the aligned circumferential positions of the particular first inner prong and particular second inner prong.
  • the billowing graft billows along the longitudinal channel.
  • the billowing graft is attached to the two first outer prongs adjacent the particular first inner prong and to the two second outer prongs adjacent the particular second inner prong.
  • the billowing graft is free to billow radially outward from and radially inward toward the particular first inner prong and the particular first inner prong along the longitudinal channel.
  • the first inner prongs have tips directed in a first longitudinal direction; and the first outer prongs have tips directed in a second longitudinal direction opposite the first longitudinal direction.
  • the first support ring further has a radially flat portion defined by at least two prongs that extend in opposite longitudinal directions, the at least two prongs of the radially flat portion of the first support ring being equidistant from the central longitudinal axis.
  • the first outer prongs and the at least two prongs of the radially flat portion of the first support ring are equidistant from the central longitudinal axis.
  • the second support ring further has a radially flat portion defined by at least two prongs that extend in opposite longitudinal directions, the at least two prongs of the radially flat portion of the second support ring being equidistant from the central longitudinal axis.
  • the radially flat portion of the first support ring has a circumferential position aligned with a circumferential position of the radially flat portion of the second support ring.
  • an angle subtended partially around the central longitudinal axis by the radially flat portion of the first support ring is approximately equal to an angle subtended partially around the central longitudinal axis by the radially flat portion of the second support ring.
  • the angle subtended partially around the central longitudinal axis by the radially flat portion of the first support ring is less than one hundred and eighty degrees.
  • first inner prongs and first outer prongs are connected together by intermediate connecting segments; and the first inner prongs, first outer prongs and intermediate connecting segments together subtend a summation angle of greater than one hundred and eighty degrees around the central longitudinal axis.
  • the first support ring comprises a first portion including the first inner prongs and first outer prongs and a second portion including the radially flat portion of the first support ring; and the first portion of the first support ring is C- shaped and subtends an angle of greater than one hundred and eighty degrees around the central longitudinal axis.
  • the second inner prongs have tips directed in the first longitudinal direction; and the second outer prongs have tips directed in the second longitudinal direction opposite the first longitudinal direction.
  • the second outer prongs have tips directed in the first longitudinal direction; and the second inner prongs have tips directed in the second longitudinal direction opposite the first longitudinal direction.
  • At least one fenestration for receiving a vessel is formed through the billowing graft.
  • a radio-opaque marker is placed around the at least one fenestration.
  • the fenestration is formed through the billowing graft at a circumferential position corresponding to a circumferential position of a radially flat portion of the first support ring and a circumferential position of a radially flat portion of the second support ring.
  • a method for forming a stent assembly inlcudes: providing a first support ring having interconnected circumferentially alternating first inner prongs and first outer prongs, the first support ring having a neutral state in which the first inner prongs define a first inner diameter around a central longitudinal axis, and in which the first outer prongs define a first outer diameter around the central longitudinal axis greater than the first inner diameter; providing a mandrel having at least one portion with a diameter greater than the first outer diameter; diametrically expanding the first support ring from the neutral state and at least partially surrounding the at least one portion of the mandrel with the first outer prongs; at least partially surrounding the first outer prongs with a graft; engaging the graft with the first outer prongs; removing the first support ring and graft from the mandrel; and permitting the first support ring to diametrically contract to the neutral state such that the graft follows a waving peripheral
  • the at least one portion of the mandrel with a diameter greater than the first outer diameter is a first longitudinal portion of the mandrel having a first mandrel diameter greater than the first outer diameter.
  • the mandrel further has a second longitudinal portion adjacent the first longitudinal portion of the mandrel.
  • the second longitudinal portion of the mandrel has a second mandrel diameter that is less than the first mandrel diameter and greater than the first inner diameter.
  • the method further comprises at least partially surrounding the second longitudinal portion of the mandrel with the first inner prongs.
  • the graft has an exterior side and an interior side and the graft has pockets defined along the interior side.
  • Engaging the graft with the first outer prongs includes inserting the first outer prongs into the pockets.
  • a stent assembly includes a first support ring, a second support ring, a first graft, and a second graft.
  • the first support ring has interconnected circumferentially alternating first inner portions and first outer portions, the first inner portions defining a first inner diameter around a central longitudinal axis, and the first outer portions defining a first outer diameter around the central longitudinal axis greater than the first inner diameter.
  • the second support ring is spaced from the first support ring along the central longitudinal axis.
  • the second support ring has interconnected circumferentially alternating second inner portions and second outer portions, the second inner portions defining a second inner diameter around the central longitudinal axis, and the second outer portions defining a second outer diameter around the central longitudinal axis greater than the second inner diameter.
  • the first graft engages the first support ring and second support ring, the first graft following a waving peripheral path at least partially around each of the first support ring and second support ring.
  • the second graft at least partially surrounds the first graft such that longitudinal tunnels are defined between first graft and second graft.
  • the second graft may be supported by a wire skeleton or stents.
  • the first inner portions of the first support ring have circumferential positions aligned with circumferential positions of the second inner portions of the second support ring; the first outer portions of the first support ring have
  • the first graft has radially depressed channels extending longitudinally at the circumferential positions of the first inner portions of the first support ring; and the longitudinal tunnels are defined between the radially depressed channels and the second graft.
  • a prosthetic device for the treatment of an anatomic organ in a patient.
  • the device includes a main body having a height and a circumference and formed from a plurality of circumferentially extending wires and configured for being received in the organ of the patient.
  • the main body defines a portion extending along a length thereof that has a reduced hoop stress relative to the remainder of the main body when in a relaxed state.
  • a covering extends over the main body and forms a billowing recess along the length of the frame in the main body due to the portion having reduced hoop stress.
  • the main body is formed from a wire frame having leg portions connected at respective apices and bases, wherein the wire frame forms a Z stent frame.
  • At least one pair of respective leg portions defines a structural feature of one of a height between a respective apex and base of the respective leg portions that is different from a height of the remaining apices and bases.
  • a distance between two respective apices or bases is different than the distance between the apices and bases of the remaining leg portions.
  • the portion having a reduced hoop stress comprises a portion of reduced thickness wire frame relative to the remaining wire frame of the main body.
  • the portion having a reduced hoop stress has a metal forming process applied thereto in order to form the portion having a reduced hoop stress.
  • the metal forming process is electropolishing a portion of the main body to form the portion having a reduced hoop stress.
  • the covering has a circumference that is less than that of the main body when the main body is in a relaxed state.
  • one or more stent or graft members are aligned longitudinally within the billowing recess.
  • the billowing recess is formed adjacent the portion having a reduced hoop stress.
  • the device includes an outer cover positioned outwardly of the cover, a tunnel being formed between the outer cover and the cover about the billowing recess such that a stent or graft member is received within the tunnel.
  • the main body defines two portions extending along a length thereof that have a reduced hoop stress relative to the remainder of the main body when in a relaxed state.
  • the two billowing recesses are formed along respective lengths of the frame in the main body due to the portion having reduced hoop stress.
  • the main body is configured for engaging with a further stent or graft member at a proximal end thereof, or at a distal end thereof.
  • the cover is oversized relative to the circumference of the main body.
  • the portion having a reduced hoop stress comprises a portion made from a different material than the remainder of the main body.
  • the different material is crimped with the remainder of the main body to form a continuous wire frame.
  • a prosthetic device for the treatment of abdominal aortic aneurysms in a patient.
  • the device includes a main body formed from a plurality of circumferentially extending wires and configured for being received in the abdominal artery of the patient.
  • At least one wire forms a Z stent frame having leg portions connected at respective apices and bases, wherein at least one pair of respective leg portions defines a structural feature of one of a height between a respective apex and base of the respective leg portions that is different from the remaining apices and bases or a distance between two respective apices or bases is different than the distance between the apices and bases of the remaining leg portions.
  • a covering is provided and has a circumference that is less than that of the main body when the main body is in a relaxed state. The covering extends over the main body when combined and forming a billowing recess in the covering due to the structural feature of the main body.
  • a method of forming a stent includes determining a desired structural characteristic of at least two portions of a stent frame main body that collectively form the entirety of the frame, selecting a construction of a first portion and a construction of a second portion, and forming the stent with the first portion and the second portion.
  • the main body defines a portion extending along a length thereof that has a reduced hoop stress relative to the remainder of the main body when in a relaxed state.
  • selecting a construction of the first portion includes electropolishing the first portion in a different manner than electropolishing the second portion.
  • selecting a construction of the first portion includes selecting a different material than a second material selected for the second portion.
  • selecting a different material includes selecting a material having a different thickness or thickness selected for the second portion.
  • selecting a construction of a first portion includes selecting a different frequency of apices for the first portion than selected for the second portion.
  • selecting a construction of a first portion includes selecting a greater height distance between respective apices than selected for the second portion.
  • selecting a construction of a first portion includes selecting one portion of a frame having a sharper bend in a respective apex than the bend in a respective apex of the second portion.
  • a prosthetic device for the treatment of an anatomic organ in a patient.
  • the device includes a main body having a height and a circumference and formed from a plurality of circumferentially extending wires and configured for being received in the organ of the patient.
  • the main body is formed from a wire frame having leg portions connected at respective apices and bases.
  • a covering extends over the main body, the covering being oversized to a circumference of the main body when the main body is in a relaxed state.
  • top-facing apices are engaged with the cover and a portion of bottom-facing apices are not engaged with the cover such that a billowing recess is formed along a length of the frame adjacent to the bottom- facing apices not engaged with the cover.
  • FIG. 1 is a perspective view of a support ring according to at least one embodiment.
  • FIG. 2 is a plan view of the support ring of FIG. 1.
  • FIG. 3 is an elevation view of a variable depression stent (VDS) frame including three support rings according to at least one embodiment.
  • VDS variable depression stent
  • FIG. 4 is a perspective view of the support frame of FIG. 3 with several arterial stents supported by longitudinal grooves.
  • FIG. 5 is a perspective view of a VDS stent assembly including a billowing graft and several arterial stents supported by longitudinal grooves according to at least one embodiment.
  • FIG. 6 is a longitudinal end plan view of the VDS stent assembly of FIG. 5.
  • FIG. 7 is an elevation view of the VDS frame of FIG. 3 and a mandrel according to at least one embodiment.
  • FIG. 8 is an elevation view of the VDS frame of FIG. 3 diametrically stretched onto the mandrel of FIG. 7 in preparation for engagement with the graft of FIG. 5.
  • FIG. 9 is an elevation view of the VDS frame of FIG. 3 engaged with the graft of FIG. 5 by pockets according to at least one embodiment.
  • FIG. 10 is a view of the interior side of the graft of FIG. 5 showing pockets for support frame engagement according to at least one embodiment.
  • FIG. 11 is an elevation view of a VDS frame according to at least one other embodiment.
  • FIG. 12 is a perspective view of an upper portion of the VDS frame of FIG. 11 with barbed stabilizing elements according to at least one embodiment.
  • FIG. 13 is a close-up view of a portion of the VDS frame of FIG. 11 with a barbed stabilizing element of FIG. 12.
  • FIG. 14 is another close-up view of a portion of the VDS frame of FIG. 11 with the barbed stabilizing elements of FIG. 12.
  • FIG. 15 is an elevation view of the VDS frame portion of FIG. 11 with the barbed stabilizing elements and a covering material.
  • FIG. 16 is an elevation view of a stent assembly that includes the VDS frame of FIG. 11 and a covering without fenestrations according to at least one embodiment.
  • FIG. 17 is an elevation view of a stent assembly that includes the VDS frame of FIG. 11 and a covering with a single fenestration according to another one embodiment.
  • FIG. 18 is an elevation view of a stent assembly that includes the VDS frame of FIG. 11 and a covering with a multiple fenestrations according to yet another one embodiment.
  • FIG. 19 is a plan view of a fenestration support ring according to at least one embodiment.
  • FIG. 20 is a perspective view of a stent frame according to at least one embodiment.
  • FIG. 21 is a perspective view of an endograft stent assembly that includes the stent frame of FIG. 20 and the graft material at least partially covered by microfibers or thrombogenic material according to at least one embodiment.
  • FIG. 22 is a perspective view of another stent frame according to at least one embodiment.
  • FIG. 23 is a perspective view of an endograft stent assembly that includes the stent frame of FIG. 22 at least partially covered by a graft.
  • FIG. 24 is an elevation view of a divided upper stent tube and two lower stent tubes of different length according to at least one embodiment.
  • FIG. 25 is a longitudinal end view of the stent tubes of FIG. 24 showing a septum dividing the upper stent tube according to at least one embodiment.
  • FIG. 26 is an elevation view of a graft tube reinforced with Z stents according to at least one embodiment.
  • FIG. 27 is an elevation view of a bifurcated stent system, according to at least one embodiment, including the stent tubes of FIG. 24 and the graft tube of FIG. 26.
  • FIG. 28 is an elevation view of a second limb stent for engagement with the shorter tube of FIG. 24 according to at least one embodiment.
  • FIG. 29 is an elevation view of a multi-branch stent assembly according to at least one embodiment.
  • FIG. 30 is an elevation view of the multi-branch stent assembly of FIG. 29 in use with the second iliac limb stent of FIG. 28.
  • FIG. 31 is a longitudinal end view of a stent assembly according to yet another embodiment in which multiple longitudinal channels defined by a first circumferential graft are covered to form tunnels by a second circumferential graft.
  • FIG. 32 is a view of the stent assembly of FIG. 31 positioned in an artery for use in treating a thoracoabdominal aneurysm.
  • FIG. 33 is a longitudinal end view of a stent assembly with an inflatable seal component according to at least one embodiment.
  • FIG. 34 is a perspective view of a stent assembly having one or more portions of reduced hoop stress relative to the remainder of the stent assembly frame according to at least one embodiment.
  • FIG. 35 is a top view of a stent assembly having one or more portions of reduced hoop stress relative to the remainder of the stent assembly frame according to at least one embodiment.
  • FIG. 36 is a front view of a stent assembly having one or more portions of reduced hoop stress relative to the remainder of the stent assembly frame, where the portion includes z-stents of increased height relative to the remainder of the stent assembly frame according to at least one embodiment.
  • FIG. 37 is a front view of a row of stent frame wire having one or more portions of reduced hoop stress relative to the remainder of the stent assembly frame, where the portion includes z-stents of increased spacing between respective apices according to at least one embodiment.
  • FIG. 38 s a front view of a series of rows of stent frame wire having one or more portions of reduced hoop stress relative to the remainder of the stent assembly frame, where the portion includes areas of reduced thickness wire relative to the remainder of the stent assembly frame according to at least one embodiment.
  • FIG. 39 is a perspective view of a stent assembly having one or more portions of reduced hoop stress relative to the remainder of the stent assembly frame according to at least one embodiment.
  • FIG. 40 is a perspective view of a stent frame having one or more portions of reduced hoop stress relative to the remainder of the stent assembly frame, where the portion includes z-stents of varying heights according to at least one embodiment.
  • FIG. 41 is a perspective view of a stent frame having one or more portions of reduced hoop stress relative to the remainder of the stent assembly frame, where the portion includes z-stents of varying heights according to at least one embodiment.
  • FIG. 42 is a perspective view of a stent frame assembly having a covering thereon, where only the apices are shown attached to the covering according to at least one embodiment.
  • FIG. 43 is a top view of the stent frame assembly of FIG. 42 according to at least one embodiment.
  • FIG. 44 is a top view of the stent frame assembly of FIG. 43 where the assembly is under pressure from blood flow according to at least one embodiment.
  • FIG. 45 is a top view of the stent frame assembly of FIG. 44 having an outer cover installed thereabout and a pair of graft members received within a billow formed by the stent frame assembly according to at least one embodiment.
  • FIGS. 1 and 2 An embodiment of a support ring 102 is shown in FIGS. 1 and 2.
  • the support ring 102 has two distinct diameters, namely an inner diameter 110 and a greater outer diameter 120, defined respectively by alternating inner prongs 112 and outer prongs 122 of the support ring.
  • the inner prongs 112 are connected to the outer prongs 122 by intermediate connecting segments 130.
  • the support ring surrounds a longitudinal axis 104, and defines a longitudinal length 106 between oppositely directed tips 114 of the inner prongs 112 and tips 124 of the outer prongs 122.
  • the support ring 102 is formed from one continuous wire.
  • segments of the support ring 112 are prongs, tips, and connecting segments for the purpose of detailing the support ring.
  • the tips 114 of the inner prongs 112 are shown as downwardly directed and the tips 124 of the outer prongs 122 are shown upwardly directed.
  • This particular orientation is depicted for exemplary purposes. Other orientations may be preferred and are within the scope of these descriptions and the drawings.
  • FIG. 3 illustrates a stent frame 400 including three support rings, each generally within the scope of the descriptions of the support ring 102.
  • the stent frame 400 includes same-oriented upper and middle support rings 102 and 202, and one oppositely oriented lower support ring 302.
  • the lower support ring 302 is illustrated as having its inner prong tips 314 upwardly directed and its outer prong tips 324 downwardly directed.
  • FIG. 3 depicts one example of multiple support rings together forming a stent frame 400 having an inner diameter 110 and a greater outer diameter 120.
  • FIG. 3 illustrates the support rings 102, 202 and 302 as approximately concentric with the longitudinal axis and spaced along the longitudinal axis 104 without expressly illustrating any interconnecting structure among the support rings.
  • the support rings in at least one embodiment are interconnected and maintained in their relative positions by a cover, for example the major cover graft 502 that generally surrounds the stent frame 400 in FIGS. 5 and 6.
  • FIGS. 4 and 5 a first longitudinal side stent 532a and a second longitudinal side stent 532b are shown in FIG. 4 as cradled within exterior longitudinal channels defined by the stent frame 400.
  • the side stents 532a and 532b are supported by the support rings in use when blood pressure is applied.
  • FIG. 5 includes also a major cover graft 502 generally surrounding the stent frame 400, between the stent frame 400 and the side stents 532a and 532b.
  • a central fluid flow channel 504 is defined within the major cover graft 502 along the longitudinal axis 104.
  • Longitudinal grooves for the side stents 532a and 532b are formed where the graft material is in contact with the side stents. Longitudinal fluid flow channels 506a and 506b are defined respectively within the side stents 532a and 532b. In other embodiments, additional parallel side stents can be included. In the stent assembly 500 of FIG.
  • blood pressure can bear upon the major cover graft 502 from within, and arterial or aortic tissue can be contacted along the exterior of the stent assembly 500, while the side stents 532a and 532b are supported and localized within the longitudinal grooves formed between the cover graft 502 and tissue by the support rings 102, 202 and 302 of the stent frame 400.
  • each support ring each subtend a circumferential angle as shown in FIG. 2.
  • Each inner prong 112 is illustrated as subtending a greater circumferential angle 116 than the circumferential angle 126 subtended by each outer prong 122.
  • Other proportions than that expressly depicted in FIG. 2 are within the scope of these descriptions. As shown best in FIG.
  • the support ring 102 further includes a radially flat portion 150, illustrated as having two commonly directed prongs 152 at the circumferential margins of the flat portion 150 and an oppositely directed central prong 154.
  • the radially flat portion 150 is distinct from other portions of the support ring 100 in that it lies in a cylindrical surface equidistant from the central longitudinal axis 104, whereas the inner prongs 112 and outer prongs 122 lie at alternating respective near and far radial distances 118 and 128 from the axis 104 with the intermediate connecting segments 130 spanning the radial difference between the near and far radial distances 118 and 128, which measure as halves of the inner and outer diameters 110 and 120 respectively.
  • the support ring has a first circumferential portion subtending a first angle 140 and defined by alternating radially inner and outer prongs 112 and 114 with respect to the longitudinal axis 104, and a second circumferential portion subtending a second angle 142 and defined by a radially flat portion 150 at a uniform distance from the central longitudinal axis 104, that uniform distance being the far radial distance 128.
  • the sum of the subtended first angle 140 and the subtended second angle 142 is equal to three hundred and sixty (360) degrees.
  • the first portion is C-shaped as defined by the summation angle 140 being greater than one hundred and eighty (180) degrees.
  • each inner prong 112 is defined by a U-shaped element having two linear longitudinally extending portions connected by the tip 114.
  • each outer prong 122 is defined by a U-shaped element having two linear longitudinally extending portions connected by the tip 124.
  • the connecting segments 130 are curvilinear, extending both longitudinally and radially. For example, when viewed along a side as shown in FIG. 3, from a view perpendicular to the longitudinal axis, the connecting segments 130 appear as S-shaped.
  • the inner prongs 112 of the support ring 102, the inner prongs 212 of the support ring 202, and the inner prongs 312 of the support ring 302 are aligned with regard to their circumferential positions.
  • the outer prongs 122 of the support ring 102, the outer prongs 222 of the support ring 202, and the outer prongs 322 of the support ring 302 are aligned.
  • the radial depressions 132 (FIG.
  • variable depression stent (VDS) frame 300 with respect to FIG. 3.
  • VDS variable depression stent
  • circumferential channels partially surround the longitudinal axis 104.
  • a first circumferential channel 434 is defined radially outward from the inner prongs 112 of the support ring 102 longitudinally between the outer prongs 122 of the support ring 102 and the outer prongs 222 of the support ring 202.
  • a second circumferential channel 434 is defined radially outward from the inner prongs 112 of the support ring 102 longitudinally between the outer prongs 122 of the support ring 102 and the outer prongs 222 of the support ring 202.
  • circumferential channel 436 is defined radially outward from the inner prongs 212 of the support ring 202 and inner prongs 312 of the support ring 302 longitudinally between the outer prongs 222 of the support ring 202 and the outer prongs 322 of the support ring 302.
  • the stent frame 400 has the inner diameter 110 along the circumferential channels 434 and 436, corresponding to the inner diameter 110 of the support rings 102, 202, 302 in those circumferential portions corresponding to the circumferential summation angle 140 (FIG. 2).
  • the stent frame 400 has the outer diameter 120 elsewhere, including full circular peripheries at the longitudinal positions of the outer prongs 122, 222 and 322, and partial circular peripheries subtending the angle 142 (FIG. 2) corresponding to the longitudinal and circumferential positions of the radially flat portions 150, 250 and 350 of the support rings.
  • the stent frame 400 has a radially flat portion 450 corresponding to the circumferential locations of radially flat portions 150, 250 and 350 of the support rings.
  • the VDS assembly 500 is shown in FIG. 6 along the longitudinal axis as viewed from above the upper longitudinal end 520 of the assembly in FIG. 5.
  • a billowing aspect of the major cover graft 502 can be understood from viewing FIG. 6.
  • a waving state of the graft 502 is seen due to the major cover graft 502 following a waving peripheral path around the stent frame 400.
  • the path length of the waving peripheral path of the major cover graft 502 is greater than an outer circumference of the stent frame 400 as prescribed by the outer diameter 120 defined by the outer prongs 122, 222 and 322 of the support rings 100, 200 and 300.
  • excess material of the graft 502 billows.
  • portions of the graft 502 overlying the circumferential positions of the exterior longitudinal channels 432 defined by the stent frame 400 are shown as billowed inward in FIG. 6. Portions of the graft 502 overlying the circumferential positions of the outer prongs 122, 222 and 322 (see also FIG. 3), are maintained radially outward from the longitudinal channels 432.
  • the graft 502 is expected to billow outwardly to contact arterial or aortic tissue along the exterior of the graft 502.
  • the side stents 532a and 532b are supported and localized within the longitudinal channels 432 between the major cover graft 502 and the tissue. This facilitates blood flow within the longitudinal fluid flow channels 506a and 506b defined within the side stents 532a and 532b.
  • the billowing properties of the graft will create a complete seal along the side stents 532a and 532b.
  • these descriptions refer to the VDS assembly 500 as having a billowing graft, referring to the billowing aspect of the major cover graft 502.
  • FIGS. 7-9 Assembly of the billowing graft VDS assembly 500, and other billowing graft VDS assemblies within the scope of these descriptions, can be understood in view of FIGS. 7-9.
  • the stent frame 400 of FIG. 3 in its neutral state is shown longitudinally aligned with a mandrel 700.
  • the mandrel 700 has alternating lesser and greater diameter portions.
  • the mandrel has circumferential channels 734 and 736 defining lesser diameter portions corresponding to the circumferential channels 434 and 436 of the stent frame 400 at the longitudinal positions of the inner prongs 112, 212 and 312 of the support rings 102, 202, 302.
  • the remainder of the mandrel 700 defines greater diameter portions corresponding to the remainder of the stent frame 400, particularly the longitudinal positions of the outer prongs 122, 222 and 322 of the support rings 102, 202, 302.
  • the lesser diameter 710 of the mandrel at the lesser diameter portions defined by the circumferential channels 734 and 736 is greater than the inner diameter 110 of the stent frame 400 in its neutral state (FIGS. 3 and 7).
  • the greater diameter 720 of the mandrel at the greater diameter portions is greater than the outer diameter 420 of the stent frame 400.
  • the stent frame 400 and each support ring 102, 202 and 302 is diametrically expanded onto the mandrel 700 in FIG. 8.
  • the stent frame 400 is ready for assembly with the graft 502 in a relatively taut condition of the graft.
  • the stent frame 400 and graft 502 are removed from the mandrel as one piece, for example by removal of the mandrel from either longitudinal end of the stent frame 400 and graft 502.
  • the stent frame 400 returns to the neutral state of FIG. 6, in which the waving state of the graft 502 is seen to show the billowing aspect of the major cover graft 502 as described with reference to FIG. 6.
  • the graft 502 generally maintains the support rings 102, 202 and 302 as approximately concentric with the longitudinal axis and spaced along the longitudinal axis as shown in FIG. 3 according to their longitudinal positions on the mandrel 700 when the graft 502 is attached.
  • the graft 502 includes pockets 516 along its interior side 518 (FIG. 10) at positions corresponding to the locations of the outer prongs 122, 222 and 322 in the diametrically expanded state of the stent frame 400 when mounted on the mandrel 700 as shown in FIG. 8.
  • the pockets 516 receive the prong tips to maintain attachment of the graft 502 to the stent frame 400, for example as shown particularly in FIG. 9 with regard to the tips 124 of the outer prongs 122 of the support ring 102 and the tips 224 of the outer prongs 222 of the support ring 202.
  • the graft 502 has circumferential excess relative to the circumference of the stent frame 400 prescribed by the outer diameter 320 when the neutral state of the stent frame is reached, for example upon removal from the mandrel 700.
  • circumferential excess of the graft 502 is circumferentially distributed as waves as seen in the graft 502 in FIG. 6, and the billowing aspect of the major cover graft 502 is distributed and facilitated along its periphery.
  • the graft 502 may be sewn to the stent frame 400 or attached in any other appropriate manner such as glue, suturing, lamination, or a mechanical fastener such as a clip. Thus, various attachment steps may be carried out while the, stent frame 400 and graft 502 are engaged with the mandrel 700.
  • the support ring 102 is made of a memory shape wire, such as nitinol. Other biocompatible materials may be used.
  • the memory shape wire is formed and heat treated in a fashion to create longitudinal and radial support.
  • the ring 102 is formed such that the outer prongs 122 exert an outward radial force.
  • the outer prongs 122 exert a higher radial force than the inner prongs 112.
  • the outer prongs 122 may have a different Austenite finish temperature ("Af ') than inner prongs 112.
  • Af ' Austenite finish temperature
  • the inner prongs 112 would be insulated/masked during a high temperature and time heat set-processing.
  • the entire ring 102 would be heated to a certain temperature before the inner prongs 112 are masked or insulated.
  • the outer prongs 122 would then be exposed to a more aggressive heat-set process to achieve a high radial force, while the masking of the inner prongs 112 would result in a lower radial force.
  • the high radial force area would have an Af ⁇ 30 degrees Celsius and the lower radial force area would have an Af somewhere in the range of 35 - 39 degrees Celsius.
  • Another method of achieving the variation in radial force may be to electropolish the entire ring 102 up to a certain point.
  • the outer prongs 122 may then be masked before further electropolishing of the inner prongs 112, thereby making the wire thinner in diameter in that section and resulting in a lower radial force. It should be appreciated that a combination of these two approaches may also be used.
  • the radial force exerted by the outer prongs 122 may vary such that the force exerted by some of the outer prongs 122 is less than the force exerted by the inner prongs 112.
  • the radial force exerted by the outer prongs 122 may vary such that the force exerted by some of the inner prongs 112 is greater the force exerted by the outer prongs 122.
  • the stent frame 400 is somewhat flexible, for example in order to stretch onto the mandrel 700, and is resilient so as to return to its neutral dimensions to facilitate the billowing aspect of the major cover graft 502.
  • the flexible and resilient properties of the stent frame 400 also facilitate that the VDS assembly 500 conforms to shapes and dimensions of surrounding biological tissue in use while the side stents 532a and 532b are supported and localized within the longitudinal channels 434 between the cover graft 502 and the tissue.
  • a stent frame according to these descriptions as flexible and resilient so as to return to neutral dimensions refers both to diametrically contracting to neutral dimensions after being diametrically expanded and diametrically expanding to neutral dimensions after being diametrically compressed.
  • the stent frame 400 upon removal from the mandrel 700, the stent frame 400, the stent frame diametrically contracts to neutral dimensions.
  • the stent frame 400 is resiliently self-biased toward neutral dimensions and bears outward force upon any outer structure or tissue that constrains the stent frame 400 to less than its neutral diameter. This feature facilitates that a VDS stent assembly including such a frame conforms to anatomical dimensions to assure against endoleaks.
  • a second self-expanding stent frame is inserted into the first self-expanding stent frame.
  • a second stent frame can be subsequently installed within the first stent frame.
  • the second self-expanding stent frame then bears gentle outward force upon the interior of the first stent frame, further supporting the stent assembly, increasing the diameter of the first stent and urging it to conform to the new anatomical dimensions.
  • the support ring 102 has eight (8) radial depressions 132 as shown in FIG. 2.
  • the support rings 202 and 302 also have eight radial depressions each, such that the stent frame 400 has eight exterior longitudinal channels 432.
  • a stent frame otherwise within the scope of these descriptions can have more than or less than eight exterior longitudinal channels.
  • Support rings 102, 202 and 302 are illustrated as having the same inner diameters such that the stent frame 400 has the same inner diameter 110 defined by the inner prongs of each support ring.
  • support rings 102, 202 and 302 are illustrated as having the same outer diameters such that the stent frame 400 has the same outer diameter 120 defined by the outer prongs of each support ring.
  • the dimensions of support rings along the length of a stent frame can vary, for example to suit the various anatomies of different patients.
  • the inner diameter 110 of the stent frame 400 is approximately thirty (30) millimeters and the outer diameter 120 is approximately thirty eight (38) millimeters. While the stent frame 400 is illustrated to have three support rings as shown in FIG. 3, other embodiments of stent frames within the scope of these descriptions can have any number of support rings.
  • the stent frame 400 is shown with a covering described as the major cover graft 502.
  • This design and variations thereof are useful, for example, in endovascular reconstruction of the aorta wherever major aortic branches are involved. This includes the ascending aorta and the coronary arteries, the aortic arch and its branches, the thoracoabdominal aorta and the visceral arteries, the common iliac artery, and the hypogastric artery. Stent frames and grafts within the scope of these descriptions are useful in these and other anatomical regions.
  • the major cover graft 502 is used on the external surface of the stent frame 400.
  • the graft 502 may be formed as covered Z stents, mesh wire, braided stents and other constructions of stent like material and biologically inert coverings (e.g. PTFE, polyester, ePTFE etc.) impermeable to blood and serum.
  • the major cover graft 502 covers the stent frame 400 partially or completely along its length or circumference. Once the graft 502 is applied to the stent frame 400, the graft 502 defines walls of the exterior longitudinal channels 432 along which different branches of the aorta may be accessed and cannulated.
  • the side stents 532a and 532b and other stents and grafts can be placed in fluid
  • aortic branches such as coronary arteries, aortic arch branches, visceral branches and hypogastric arteries.
  • a fenestration 510 is formed through the major cover graft 502 of the VDS assembly 500 to receive a vessel 512, which represents an artery such as a superior mesenteric artery (SMA) or a stent or stent graft.
  • the fenestration 510 permits fluid flow from the central fluid flow channel 504 to enter the vessel 512, defining a lateral flow channel 514 through the major cover graft 502 at the fenestration 510 and along the vessel 512.
  • Such fenestrations may be located anywhere along the graft 502 where technically feasible with respect to the support rings within the graft.
  • the fenestration 510 is located at the front center of the frame.
  • the fenestration 510 and other fenestrations formed to access fluid communication with the central fluid flow channel 504 may have various diameters and may be shaped as circular, oval, or other shapes.
  • the fenestration 510 represents an opening formed through the material of the major cover graft 502 in a location that does conflict with the support rings of the stent frame.
  • the fenestration 510 is formed at a longitudinal and
  • the fenestration 510 for an SMA vessel, stent, or graft is formed at a circumferential location corresponding to the radially flat portion 450 of the stent frame 400.
  • stent frame 400 is illustrated to have three support rings as shown in FIG. 3, other embodiments of stent frames within the scope of these descriptions can have any number of support rings.
  • support ring 102 has alternating inner prongs 112, outer prongs 122, radial depressions 132, and a radially flat portion 150, other embodiments of support rings within the scope of these descriptions can have other geometric configurations.
  • a stent frame 800 according to at least one embodiment is shown in FIG. 11.
  • the stent frame 800 includes, in order from top to bottom in the drawings, a first frustoconical support ring 810, a first single diameter support ring 820, the support ring 102, the support ring 302, a second frustoconical support ring 830, a second single diameter support ring 840, and a third single diameter support ring 850.
  • the stent frame 800 is configured to support a multi-path stent assembly having a longitudinal axis 802 along which a central fluid flow channel 804 is defined for blood flow in a downstream direction from a first end defined by the first frustoconical support ring 810 to a second end defined by the third single diameter support ring 850.
  • the stent frame 800 advantageously has a first diameter reduction at the first frustoconical support ring 810 and a second diameter reduction at the second frustoconical support ring 830, such that flow along the central fluid flow channel 804 may be reduced by one or more flow channels that branch from the central fluid flow channel 804 in a stent assembly supported by the stent frame 800.
  • frustoconical support ring 810 constitutes the cranial end of the stent frame 800 with reference to human anatomy, and the second longitudinal end defined by the third single diameter support ring 850 constitutes the caudal end of the stent frame 800.
  • the first frustoconical support ring 810 is formed as a Z-stent having a first end 812 with a diameter greater than that of a second end 814.
  • the first end 812 is defined by turning points of the Z-stent extending outward from the longitudinal axis 802.
  • the second end 814 is defined by turning points of the Z-stent extending inward from the longitudinal axis 802.
  • the single diameter support ring 820 is formed as a Z-stent in which turning points are equidistant from the longitudinal axis 802.
  • the support ring 102 and the support ring 302 are detailed in the preceding descriptions with reference to FIGS. 1-3.
  • the second frustoconical support ring 830 is formed as a Z-stent having a first end 832 with a diameter greater than that of a second end 834.
  • the first end 832 is defined by turning points of the Z-stent extending outward from the longitudinal axis 802.
  • the second end 834 is defined by turning points of the Z-stent extending inward from the longitudinal axis 802.
  • the single diameter support rings 820, 840, and 850 are formed as Z-stents in which respective turning points are equidistant from the longitudinal axis 802, defining a single respective diameter for each ring.
  • the second and third single-diameter support rings 840 and 850 are illustrated having the same diameter in the stent frame 800.
  • the first single diameter support ring 820 is illustrated as having greater diameter than the second and third single-diameter support rings 840 and 850, which are downstream of the diameter-reducing second frustoconical support ring 830 relative to the first single diameter support ring 820.
  • the stent frame 800 can be covered with a variety of coverings, at least three of which are represented in FIGS. 16-18.
  • the illustrated upper end represents the upstream longitudinal end of the stent assembly
  • the illustrated lower end represents the downstream longitudinal end.
  • each serves as an endograft in which blood flows downstream through the longitudinal central channel of the stent assembly from a greater diameter upstream end to a lesser diameter downstream end, and one or more branches may direct blood flow from the central channel.
  • the upstream end constitutes the cranial end of the stent frame 800 with reference to human anatomy
  • the downstream end constitutes the caudal end of the stent frame 800.
  • stabilizing elements may be connected to the first frustoconical support ring 810 as shown in FIGS. 12- 15.
  • stabilizing elements 860 extending from the upstream end of the support ring 810 define a crown for engaging tissue.
  • each stabilizing element 869 is wrapped around a respective prong 816 of the support ring 810 and formed from memory shape wire or stainless steel wire.
  • Each stabilizing element 860 includes a barb 862 or hook that is uncovered and serves to fixate the endograft and add stability against the aortic wall.
  • Each stabilizing element 860 also includes a limb 864 (FIG. 13) that is covered by the covering material 870 in FIG. 15. As shown in FIG. 13-14, the limb 864 is positioned between the prongs 816 of the support ring 810.
  • the attachment point 866 of the stabilizing element 860 acts as a fulcrum for the limb 864.
  • the barbs 862 engage the aorta, while the limbs 864 push outward against the covering material 870 as shown in FIG. 15 to seal the covering material 870 against the aorta. In that way, the limbs 864 act as biasing elements.
  • the covering material 870 represents, for example, the upper end of any one of the coverings shown in FIGS. 16-18.
  • Each stabilizing element 860 may be formed separately from stainless steel or other metal. It can be laser cut in whole together with the support ring 810. The stabilizing elements 860 may be individually wrapped around a prong 816. The shape of the element 860 as depicted allows for one end of the wire to "hook" into the aortic wall, thereby stabilizing the device and preventing migration of the endograft. The caudal end of the limb 864 will have an eccentrically directed angle and this portion of the wire will be located on the inside aspect of the graft coverage, in this embodiment the PTFE.
  • the endograft coverage will be pushed externally against the aortic wall to create additional points of contacts and seal.
  • the limbs 864 are captured towards the center of the graft with the delivery system, they can restrain the top stent and make the device easier to control.
  • a stent assembly 900 includes the stent frame 800 and a covering 902 sheathing the stent frame.
  • the covering 902 is shown without any fenestrations.
  • the stent assembly 900 can be used below the kidney vessels.
  • a stent assembly 1000 includes the stent frame 800 and a covering 1002 sheathing the stent frame.
  • the covering 1002 is shown with a single fenestration 1004 illustrated as a rectangular slot in the cranial end of the covering 1002.
  • the slot has an open cranial end 1006 such that the upper edge of the covering 1002, interrupted by the open cranial end of the slot, partially surrounds the frame 800.
  • the stent assembly 1000 can be used for aneurysms below the superior mesenteric artery (SMA).
  • SMA superior mesenteric artery
  • the single fenestration 1004 is used for both celiac artery and SMA stents or grafts.
  • a stent assembly 1100 includes the stent frame 800 and a covering 1102 sheathing the stent frame.
  • a first fenestration 1104 is illustrated as a rectangular slot in the cranial end of the covering 1102, in which the slot has an open cranial end 1106 such the upper edge of the covering 1102, interrupted by the open cranial end of the slot, partially surrounds the frame 800.
  • a second fenestration 1110 is illustrated as a circular hole in the covering 1102.
  • the stent assembly 1100 can be used for aneurysms below the celiac artery.
  • the first fenestration 1104 and the separate second fenestration 1110 are used respectively as separate access fenestrations for the celiac artery and SMA stents or grafts.
  • a portion of the far side of the stent frame is visible through the fenestration 1110
  • a fenestration support ring 1120 surrounds the second fenestration 1110.
  • the fenestration support ring 1120 can be, for example, an eight (8) millimeter diameter ring formed from nitinol or other biocompatible materials, or can be constructed, for example, as described below with reference to FIG. 19.
  • the fenestration support ring 1120 placed around the second fenestration 1110 in FIG. 18, the fenestration support ring 1120 in at least one use receives and stabilizes the fenestration support of a branch in fluid communication with the stent assembly 1100 such as an SMA vessel or an SMA stent or graft.
  • the fenestration support ring 1120 may also serve as a radio-opaque marker during the placement procedure of the stent assembly 1100.
  • the fenestration support ring 1120 serves as "point zero" for the positioning and deployment of the stent assembly 1100, or any stent assembly in which the fenestration support ring 1120 is included.
  • the fenestration support ring 1120 for such use can be constructed of or with materials visible under X-ray or other medical imaging techniques.
  • the fenestration support ring 1120 constructed as illustrated can serve as a radio-opaque marker.
  • the fenestration support ring 1120 in this embodiment includes two supports 1122 formed as half-circles from a memory shape wire. Nitinol and/or other materials with the similar properties can be used to form the half-circle supports.
  • the supports 1122 are wrapped with singular or multiple turns 1124 of a thin radio-opaque marker material such as platinum.
  • the supports 1122 are connected by crimping their ends with connectors 1126.
  • each connector 1126 is formed from gold, which also acts as a radio-opaque marker.
  • the fenestration support ring 1120 therefore illustratively stabilizes the fenestration 1110 and makes the fenestration visible on an x-ray image.
  • the marker 1120 may be connected to the frame 800 via glue or other adhesive, stitching, or heat treatment.
  • FIG. 20 is a perspective view of a stent frame 1200 according to at least one embodiment.
  • FIG. 21 is a perspective view of an endograft stent assembly 1300 that includes the stent frame 1200 at least partially covered by a graft 1304.
  • the design and geometrical shape of the endograft stent assembly 1300 permits separate access to the renal arteries, thus facilitating use with many anatomical variations of juxtarenal and suprarenal aneurysms.
  • the design allows for placement of parallel covered renal stents while reducing the likelihood of an endoleak along the renal stents, and reduces the risk of kinking and compression of the renal stents.
  • the stent frame 1200 can be constructed of a metal alloy, including a memory shape wire such as nitinol. Other biocompatible materials may be used. In at least one example, the memory shape wire is cut and heat treated in a fashion to create longitudinal and radial support.
  • the stent frame 1200 includes circumferential wires 1202 shaped to define circumferential waves that are aligned longitudinally to define longitudinal channels.
  • a radial variation is defined between the crests (radial maxima) and nadirs (radial minima) of the circumferential waves.
  • the radial variation is approximately three (3) millimeters.
  • the radial variation may be in the range of two to four (2- 4) millimeters.
  • the circumferential distance between the crests can be, for example, in the range of three to fifteen (3-15) millimeters.
  • the stent frame 1200 has a radially flat portion for locating an SMA vessel, stent, or graft that branches from the interior of the endograft stent assembly 1300.
  • the stent frame 1200 includes longitudinal wires 1204 that extend between the circumferential wires.
  • Each circumferential wire 1202 is spaced, for example at 5-20mm, from the next and has a wave shape to define the longitudinal channels.
  • the circumferential positions of the longitudinal wires 1204 alternate in a staggered fashion.
  • the endograft stent assembly 1300 includes a fenestration support ring 1320, which, in the illustrative embodiment, is an 8mm nitinol ring.
  • the fenestration support ring 1320 is positioned or created within the stent frame 1200 with its center point at
  • the fenestration support ring 1320 in at least one use receives the visceral or SMA stent placed during the placement procedure.
  • the fenestration support ring 1320 also serves as "point zero" for the positioning and deployment of the endograft stent assembly 1300.
  • a second ring (not shown) may be positioned cranial of the SMA fenestration support ring 1320, with its center approximately fifteen (15) millimeters cranial to the fenestration support ring 1320.
  • the center of the second ring may be at 12:30 clock position relative to the SMA fenestration support ring 1320, and the diameter of the second ring may measure between eight and ten (8-10) millimeters.
  • the stent frame 1200 may be formed as one unit. In at least one embodiment the stent frame 1200 approximately one hundred (100) millimeters in longitudinal length.
  • the proximal aspect of the stent frame 1200 is wavy tubular extending thirty four (34) millimeters proximal to the center point of the visceral or SMA fenestration support ring 1320.
  • the distal aspect extends fourteen (14) millimeters below the center point of the SMA fenestration support ring.
  • the stent frame 1200 includes a distal extension 1210 that funnels to eighteen (18) millimeters or more in diameter over a distance often to twenty (10-20) millimeters.
  • This distal extension 1210 is approximately fifty to sixty (50-60) millimeters long, with at least the most distal forty (40) millimeters measuring at least eighteen (18) millimeters in diameter.
  • the most anterior portion of the proximal part of this stent frame 1200 is curved flat and does not have any waves or channels.
  • the stent frame 1200 includes a crown of barbed stents 1220 extending from its top edge 1222 at its most cranial aspect.
  • the barbed stents 1220 are uncovered and serve to fixate the endograft stent assembly and add stability against the aortic wall.
  • Each barbed stent 1220 is formed of memory shape wire.
  • the barbed stents 1220 are formed in a figure-of-eight fashion with the top of the component containing a hook facing the external surface of the stent.
  • the hook may be attached to the proximal end of a wire.
  • the middle of the wire is equipped with a small round hole for placement of a trigger wire.
  • the barbed stents 1220 are shaped to extend outwards to a 45 degree angle on the horizontal plane upon deployment.
  • the graft 1304 is partially covered with microfibers or other thrombogenic material 1310 along the 3 and 9 o'clock aspects of it, with the center of the fenestration support ring 1320 defining 12 o'clock.
  • the microfibers 1310 assist in filling any remaining gutters as a source of endoleak along parallel renal stents.
  • hydrogel or other sealing materials may be used to coat the external surface of the endograft in order to fill in any gutters alongside the parallel renal stents.
  • a fenestration 1330 is defined by the graft 1304 as a rectangular slot in the cranial end of the graft, in which the slot has an open cranial end.
  • a second fenestration is illustrated as a circular hole in the graft 1304 in a location corresponding to the SMA fenestration support ring 1320.
  • the fenestration 1330 and the separate second fenestration are used respectively as separate access fenestrations for the celiac artery and SMA stents or grafts.
  • FIG. 22 is a perspective view of a stent frame 1400 according to at least one embodiment.
  • FIG. 23 is a perspective view of an endograft stent assembly 1500 that includes the stent frame 1400 at least partially covered by a graft 1502.
  • FIGS. 24 through 28 illustrate components of an iliac limb assembly 1600. All dimensions given in these descriptions correspond at least to one embodiment without limiting the scope of these descriptions to one such embodiment.
  • a dual channel tubular stent including graft material, such as ePTFE, supported by Z-stents.
  • the dual channel stent has two internal channels separated longitudinally by a septum 1602, for example for a distance of five (5) millimeters or more.
  • the septum 1602 is shown in longitudinal end view in FIG. 25.
  • the diameter of the upstream dual channel part of the tubular stent is twenty six (26) millimeters to twenty eight (28) millimeters in at least one example.
  • the main tube divides, for example after the first five (5) millimeters, into two approximately cylindrical tubes 1604 and 1606, one longer than the other, each measuring approximately thirteen (13) millimeters in diameter in at least one example.
  • the longer tube 1604 extends in at least one example for a distance of at least one hundred (100) millimeters.
  • the shorter tube 1606 extends in at least one example for approximately twenty (20) millimeters.
  • the longer tube 1604 constitutes a first iliac limb stent for connecting a first side or channel of the dual channel tubular stent to a first iliac artery.
  • the shorter tube 1606 constitutes a junction by which a second iliac limb stent 1608 (FIG. 8), for connection to a second iliac artery, can be connected to the second side or channel of the dual channel tubular stent.
  • FIG. 26 A graft tube 1610 reinforced with Z stents is shown in FIG. 26.
  • FIGS. 24 and 26 By placing the graft tube 1610 (FIG. 26) around the upstream dual channel part of the tubular stent (FIG. 24) produces an iliac bifurcation device 1600 (FIG. 27) that can be moved cranially and caudally within the main body of the endograft 1500 shown in FIG. 23. This will help in controlling and adjusting the location of the placement of the iliac limb stents 1604 and 1608 in the iliac arterial system.
  • FIG. 28 shows the second iliac limb stent 1608 for engagement with the shorter tube 1606 in FIG. 24.
  • the second iliac limb stent 1608 By placing the iliac bifurcation at a maximum cranial location possible within the iliac limb system as illustrated and described here, there is room to move the second iliac limb stent 1608 up or down and adjust the desired length remaining for engagement with an iliac artery.
  • the two flow channels for the two iliac limb stents 1604 and 1608 are separated by the septum 1608 throughout the upstream dual channel part of the tubular stent.
  • the septum 1602 prevents the upstream cranial end of the second iliac limb stent 1608, as the position of the stent 1608 is adjusted, from obstructing the flow entering the first iliac limb stent 1604 on the other side of the septum 1602. This permits a range of human anatomy dimensions to be served by one set of components (FIGS. 24-28).
  • FIG. 29 illustrates a multi-branch stent assembly 1700 in a state of partial assembly or installation, with the longer first iliac limb stent 1604 in engagement, at its caudal downstream end, with a first iliac artery.
  • FIG. 30 illustrates the multi-branch stent assembly 1700 of FIG. 29, in use in a human aorta, with the second iliac limb stent 1608 in engagement, at its caudal downstream end, with the second iliac artery.
  • the multi-branch stent assembly 1700 includes the stent assembly 1000 of FIG. 17.
  • the stent assembly 1000 is first installed.
  • a fenestration support ring or other radio-opaque marker serves as "point zero" for the positioning and deployment of the stent assembly 1000, during the placement procedure in order to properly place the stent assembly for engagement with the anatomical SMA and celiac artery.
  • the first iliac limb stent 1604 can be positioned in different locations by the telescoping engagement of the upstream end of the dual channel tubular stent with the downstream end of the stent assembly 1000.
  • the adjustable telescoping engagement of the dual chamber stent with the stent assembly 1000 defines a functional length adjustment for the first iliac limb stent 1604 relative to the engage first iliac limb artery.
  • the position of the dual chamber tubular stent is selected to engage the first iliac limb stent 1604 with the first iliac limb artery.
  • the second iliac limb stent 1608 can be engaged with the second iliac artery as shown in FIG. 30.
  • an endovascular device for treatment of complex abdominal aneurysms involving the kidney vessels.
  • the device can go above the kidney vessels, while blood flows to the kidneys and the gut vessels are preserved.
  • the aortic endograft does not crush the kidney stents or create gutters that may otherwise cause leaks of blood alongside the grafts.
  • FIG. 31 is a longitudinal end view of a tunneled graft stent assembly 1800 according to yet another embodiment in which multiple longitudinal channels defined by a first circumferential graft are covered by a second circumferential graft 1802 to form tunnels.
  • open longitudinal channels 432 are defined along the exterior of the graft 502, and the longitudinal side stents 532a and 532b may be laterally supported by the aortic wall in some uses.
  • the graft 502 is further covered by a second graft 1802 and covered longitudinal tunnels 1832 are defined between the inner graft 502 and outer graft 1802.
  • the covered longitudinal tunnels 1832 may constitute stents or receiving stents therein in FIG.
  • tunneled graft stent assembly 1800 parallel flow channels defined in the longitudinal tunnels don't require further lateral support and thus the tunneled graft stent assembly 1800 may be placed within an aneurysm.
  • device 1800 is shown for thoracoabdominal device placement. As illustrated, device 1800 is placed in a thoracoabdominal area and renal stents 1850 are extending into the tunnels 1832, and the celiac 1854 and SMA 1856 are also received within the device. Members 1608 interconnect the iliac arteries as previously described. In this manner, the parallel stents 1850 don't need lateral support and this allowed the device 1800 to be placed in the middle of an aneurysm.
  • FIG. 33 is a longitudinal end view of a stent assembly 1900 with an inflatable seal component 1902 according to at least one embodiment.
  • the stent assembly 1900 has an inflatable component 1902 on a graft 1904.
  • the inflatable component 1902 has a deflated state and an inflated state.
  • the assembly 1900 with one or more inflatable seal components 1902 can be put in place, with the inflatable component 1902 in its deflated state, together with parallel stents 1906.
  • longitudinal grooves are formed around the parallel stents 1906.
  • the infusion of the inflatable component 1902 with special polymers while the parallel stents 1906 are in place will create longitudinal grooves along the parallel stents 1906 after the polymers harden inside the inflatable component 1902.
  • FIGS. 34 through 45 represent various embodiments of frame assemblies for use herein. Each of the assemblies will be further described herein.
  • FIGS. 34 and 35 illustrate a prosthetic device 2010 for the treatment of an anatomic organ in a patient.
  • the prosthetic device 2010 may be used with or as a
  • the prosthetic device 2010 may include a main body 2012 having a height and a circumference and formed from a plurality of circumferentially extending wires 2014.
  • the main body 2012 may be configured for being received in the organ of the patient and is formed from a wire stent frame 2018.
  • the main body 2012 defines a portion 2016 extending along a length thereof that has a reduced hoop stress relative to the remainder of the main body 2012 when in a relaxed state.
  • length thereof may mean a height of the prosthetic device 2010 along a longitudinal or elongated direction.
  • a covering 2020 extends over the main body 2012 and forms a billowing recess 2022 along the length of the main body 2012 due to the portion having reduced hoop stress.
  • a graft assembly 2024 may be provided within the billowing recess 2022.
  • the graft assembly 2024 may be similar to graft tube 532a and 532b as already described herein.
  • the main body 2012 is formed from a wire frame 2014 having leg portions 2026 connected at respective apices 2028 and bases 2030, wherein the wire frame forms a z-stent frame.
  • the one or more portions 2016 having a reduced hoop stress relative to a remainder of the main body when in a relaxed state may be accomplished in a variety of manners.
  • at least one pair of respective leg portions 2026 defines a structural feature of one of a height HI between a respective apex 2028 and base 2030 of the respective leg portions 2026 that is different from a height H2 of the remaining apices 2028 and bases 2030.
  • an area of reduced hoop stress is formed along a medial portion of a height (instead of aligned with a height as the feature illustrated in FIG. 34) to form a billow that extends circumferentially around the main body 2012.
  • a distance Dl between two respective apices 2028 or bases 2030 is different than the distance D2 between the apices 2028 and bases 2030 of the remaining leg portions as illustrated in FIG. 37.
  • This difference between distance Dl and distance D2 may be formed by reducing the angle formed between respective apices 2028 and bases 2030, by having different material having altered structural characteristics within portion 2016, by electropolishing or providing other metal fabrication or processing of the frame in portion 2016, by having the wireframe within portion 2016 having a smaller or larger thickness relative to the remainder of the wire frame 2012, or any other method that provides a portion 2016 having a different structural or mechanical characteristic than the remainder of the wire frame 2012.
  • a first row 2040 of z-stents has a greater thickness than a second row 2042 of z-stents.
  • a billow is created that extends circumferentially around the main body 2012.
  • a portion 2042 of main body 2012 is formed due to stent construction in order to reduce the hoop stress thereabout. This may provide a billowed area that is advantageously provided for receiving or engageably nesting with a graft or other stent member.
  • the graft cover 2020 will be in contact with the aortic wall when installed.
  • Stent portion 2012' has a larger diameter sized according to the size of the aorta and will exert radial force against the graft coverage and the aorta thereby stabilizing the endograft in place within the aorta and push the cloth of the endograft against the aorta so blood does not leak around it.
  • Stent portion 2012" is of a smaller diameter and since it will be loose because of its smaller size, it must be suspended to the two stent portions 2012' and 2012"' immediately above and below it with rings, welding and other methods.
  • the virtual space 2042 that now is created allows placement of parallel stents on each respective side outside and along the main endograft without the parallel stents being crushed.
  • the graft material will billow out because of the hydrostatic pressure within the graft when implanted in the aorta, thereby pushing the graft coverage to encircle the parallel stent.
  • a continuous ring of a stent wire frame 2012 may have a portion defined between respective apices 2028 and bases 2030 that is a certain height HI and a portion defined between respective apices 2028 and bases 2030 that is a certain height H2 that is different than height HI .
  • the embodiment illustrated in FIG. 40 includes apices 2028 and bases 2030 that have a triangular shaped intersection between respective leg portions.
  • An embodiment is illustrated in FIG. 41 in which the intersection between apices 2028 and bases 2030 is generally arcuate shaped.
  • FIGS. 42 through 45 illustrate one or more embodiments of a stent design 2110 in which at least one ring of a wire frame 2112 is provided.
  • the embodiment illustrated is one of a single continuous wire frame having one row of z-stent frames, but any number of frame rows in any orientation may be equally applicable.
  • the wire frame 2112 may include leg members 2128 that span respective bases 2128 and apices 2130. In the illustrated embodiment, only the apices 2130 are crimped or otherwise engaged with cover 2120 via attachment members 2132. In this manner, the bases 2126 are not engaged with the cover 2120.
  • FIG. 43 an overhead view of the stent design 2110 of FIG. 42 when the stent design 2110 is in an unpressurized state.
  • Billows 2122 are formed when the cover 2120, which is oversized relative to the circumference of the stent 2110 when in a relaxed state, is installed about the wire frame 2112. The intersection points of each billow 2122 are formed at about the apices 2030 that are engaged with the cover 2120.
  • the stent 2110 in a pressurize state is shown in FIG. 44.
  • the pressurized state represents how the stent frame 2112 appears once installed within a patient where bloodflow occurs through the stent frame 2112.
  • the stent 2110 and cover 2120 produces a flower shape when viewed from an overhead perspective.
  • a physician selects a graft member and places next to an outward billow 2122 where a graft member is desired to run along a length or height of the stent 2110.
  • two graft members 2124 are positioned about respective billows 2122 and then placed within the aorta against the aortic wall 1.
  • the graft members are aligned longitudinally within the billowing recesses 2122.
  • the main body 2110 defines two portions 2116 extending along a length thereof that have a reduced hoop stress relative to the remainder of the main body 2110 when in a relaxed state, and further wherein two billowing recesses 2122 are formed along respective lengths of the frame 2112 in the main body 2110 due to the portion having reduced hoop stress.
  • FIGS. 34 through 45 are advantageously provided for use with the one or more prosthetic devices disclosed herein.
  • the device 2010 or 2110 may be engaged with a further prosthetic or stent member at a distal or proximal end thereof.
  • one or more methods and one or more stents made according to the one or more methods in which the stents exhibit improved structural characteristics over conventional stents or other stents used in manufacturing endografts For each method step listed, a corresponding stent structure may be made according to the method described.
  • one or more methods of forming a stent may include determining a desired structural characteristic of at least two portions of a stent frame that collectively form the entirety of the frame or a circumferential row of a row of the frame.
  • the one or more characteristic may be any desired structural characteristic, such as, for example, rigidity, flexibility, compressibility, radial strength, axial strength, smoothness of finish, and the like.
  • the method may also include selecting a first material for a first portion and a second material for a second portion. Alternatively, similar materials may be selected but different finishing processes may be used to reach a desired structural characteristic.
  • the method may also include forming the stent with the first and second material.
  • material may include a type of material, a finishing process applied to a material, a size, dimension, or similar of a material, or a shape of a material.
  • selecting a first material includes electropolishing a first material in a different manner that electropolishing a second material.
  • This may advantageously provide for a different thickness of frame material for prolonged electropolishing, or may provide for a different smoothness or texture of finish.
  • Such a selection will impact the radial and axial strength of the stent, as well as the weight and finish characteristics.
  • FIG. 37 A representative example of one form of electropolishing compared to an above-standard form of electropolishing is illustrated in FIG. 37 as follows. Specifically, as illustrated, FIG. 37 illustrates the exact same material forming the entire loop of stent frame, except that the middle portion has been electropolished at a greater intensity than each respective end portion.
  • selecting a first material may include selecting one portion of the frame have a different material than a second material.
  • consecutive rows in a stent could be made from different materials having different structural characteristics.
  • the first portion of material could have a different thickness or thickness than the second material.
  • a given row of frame material could have one portion that has a different thickness than a second portion due to electropolishing one portion more or from joining materials of different thickness.
  • the method may include selecting one portion of a frame having a different frequency of apices than a second material.
  • the first and second material or portions may be engaged by any appropriate mechanism, including welding, crimping, soldering, and the like.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Gastroenterology & Hepatology (AREA)
  • Pulmonology (AREA)
  • Prostheses (AREA)

Abstract

L'invention concerne un dispositif prothétique pour le traitement d'un organe anatomique chez un patient. Le dispositif prothétique comprend un corps principal ayant une hauteur et une circonférence, et formé à partir d'une pluralité de fils s'étendant de façon circonférentielle, et conçu pour être reçu dans l'organe du patient, le corps principal définissant une partie s'étendant le long de sa longueur qui a une contrainte circonférentielle réduite par rapport au reste du corps principal lorsqu'il est dans un état relâché, et un couvercle s'étendant sur le corps principal et formant un renfoncement circulaire le long de la longueur du cadre dans le corps principal en raison du fait que la partie a une contrainte circonférentielle réduite. L'organe anatomique peut être une aorte d'un patient.
PCT/US2015/015959 2013-06-05 2015-02-13 Ensembles greffon circulaire formés à partir d'un ou plusieurs éléments structuraux sélectionnés de façon avantageuse WO2015126768A1 (fr)

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US201461940867P 2014-02-18 2014-02-18
US61/940,867 2014-02-18

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PCT/US2014/041185 Continuation WO2014197743A1 (fr) 2013-06-05 2014-06-05 Endoprothèses à dépression variable (vds) et ensembles-greffons circulaires

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Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN108024863A (zh) * 2015-09-01 2018-05-11 美敦力公司 包括向冠状动脉提供血流的通道的支架组件以及递送和部署这种支架组件的方法
WO2018220043A1 (fr) * 2017-05-31 2018-12-06 Jotec Gmbh Endoprothèse à poches
US20210236260A1 (en) * 2018-04-30 2021-08-05 Board Of Regents Of The University Of Nebraska Stent-graft

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US5395390A (en) * 1992-05-01 1995-03-07 The Beth Israel Hospital Association Metal wire stent
US6174328B1 (en) * 1992-02-21 2001-01-16 Boston Scientific Technology, Inc. Intraluminal stent and graft
US6776793B2 (en) * 1995-03-01 2004-08-17 Scimed Life Systems, Inc. Longitudinally flexible expandable stent
US20120123524A1 (en) * 2002-12-16 2012-05-17 Boston Scientific Scimed, Inc. Flexible Stent With Improved Axial Strength
US20130116773A1 (en) * 2011-11-09 2013-05-09 Cook Medical Technologies Llc Diameter reducing tie arrangement for endoluminal prosthesis

Patent Citations (5)

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Publication number Priority date Publication date Assignee Title
US6174328B1 (en) * 1992-02-21 2001-01-16 Boston Scientific Technology, Inc. Intraluminal stent and graft
US5395390A (en) * 1992-05-01 1995-03-07 The Beth Israel Hospital Association Metal wire stent
US6776793B2 (en) * 1995-03-01 2004-08-17 Scimed Life Systems, Inc. Longitudinally flexible expandable stent
US20120123524A1 (en) * 2002-12-16 2012-05-17 Boston Scientific Scimed, Inc. Flexible Stent With Improved Axial Strength
US20130116773A1 (en) * 2011-11-09 2013-05-09 Cook Medical Technologies Llc Diameter reducing tie arrangement for endoluminal prosthesis

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN108024863A (zh) * 2015-09-01 2018-05-11 美敦力公司 包括向冠状动脉提供血流的通道的支架组件以及递送和部署这种支架组件的方法
WO2018220043A1 (fr) * 2017-05-31 2018-12-06 Jotec Gmbh Endoprothèse à poches
US11484399B2 (en) 2017-05-31 2022-11-01 Jotec Gmbh Stent graft with pockets
US20210236260A1 (en) * 2018-04-30 2021-08-05 Board Of Regents Of The University Of Nebraska Stent-graft

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