US20110029064A1 - Flexible stent - Google Patents
Flexible stent Download PDFInfo
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- US20110029064A1 US20110029064A1 US12/884,514 US88451410A US2011029064A1 US 20110029064 A1 US20110029064 A1 US 20110029064A1 US 88451410 A US88451410 A US 88451410A US 2011029064 A1 US2011029064 A1 US 2011029064A1
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- 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
- A61F2/88—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 formed as helical or spiral coils
-
- 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
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/962—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve
- A61F2/966—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve with relative longitudinal movement between outer sleeve and prosthesis, e.g. using a push rod
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/91525—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other within the whole structure different bands showing different meander characteristics, e.g. frequency or amplitude
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/91533—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other characterised by the phase between adjacent bands
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/9155—Adjacent bands being connected to each other
- A61F2002/91558—Adjacent bands being connected to each other connected peak to peak
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0028—Shapes in the form of latin or greek characters
- A61F2230/0054—V-shaped
Definitions
- the present invention relates generally to expandable tubular structures capable of insertion into small spaces in living bodies and, more particularly, concerns a stent structure which is capable of substantial and repeated flexing at points along its length without mechanical failures and with no substantial changes in its geometry.
- a stent is a tubular structure that, in a radially compressed or crimped state, may be inserted into a confined space in a living body, such as an artery or other vessel. After insertion, the stent may be expanded radially to enlarge the space in which it is located. Stents are typically characterized as balloon-expanding (BX) or self-expanding (SX).
- BX balloon-expanding
- SX self-expanding
- a balloon-expanding stent requires a balloon, which is usually part of a delivery system, to expand the stent from within and to dilate the vessel.
- a self expanding stent is designed, through choice of material, geometry, or manufacturing techniques, to expand from the crimped state to an expanded state once it is released into the intended vessel. In certain situations higher forces than the expanding force of the self expanding stent are required to dilate a diseased vessel. In this case, a balloon or similar device might be employed to aid the expansion
- Stents are typically used in the treatment of vascular and non-vascular diseases. For instance, a crimped stent may be inserted into a clogged artery and then expanded to restore blood flow in the artery. Prior to release, the stent would typically be retained in its crimped state within a catheter and the like. Upon completion of the procedure, the stent is left inside the patient's artery in its expanded state. The health, and sometimes the life, of the patient depend upon the stent's ability to remain in its expanded state.
- stents are flexible in their crimped state in order to facilitate the delivery of the stent, for example within an artery. Few are flexible after being deployed and expanded. Yet, after deployment, in certain applications, a stent may be subjected to substantial flexing or bending, axial compressions and repeated displacements at points along its length, for example, when stenting the superficial femoral artery. This can produce severe strain and fatigue, resulting in failure of the stent.
- stent-like structures A similar problem exists with respect to stent-like structures.
- An example would be a stent-like structure used with other components in a catheter-based valve delivery system. Such a stent-like structure holds a valve which is placed in a vessel.
- a stent or a stent-like structure is constructed to have different types of tubular portions along its length.
- there are strut portions and helical portions where the strut portions are constructed primarily to provide radial expansion and radial strength, and the helical portions are constructed primarily to permit repeated flexing and axial compression and expansion.
- the flexing and axial compression are likely to be required simultaneously, so the stent structure permits repeated and substantial flexing while in an axially compressed or expanded state, and it permits axial compression while in a flexed state.
- strut portions are provided between helical portions or helical portions are provided between strut portions.
- the stent is self-expanding and strut portions and helical portions alternate along the length of the stent.
- the stent is preferably constructed so that, in the expanded state the helical portions permit axial compression or expansion of about 20% (preferably between 15% and 25%) and simultaneously permit bending with a minimum bending radius of about 13 mm (preferably between 10 mm and 16 mm).
- a helical portion is made of helical elements which extend helically about the axis of the stent between points on two different strut portions which are spaced apart circumferentially by a distance which is more than approximately 25% of the circumference of the stent (which is equivalent to an extent of 90 degrees about the axis of the stent) when it is in its expanded state.
- a helical portion is made of helical elements which extend helically about the axis of the stent between locations on two different strut portions.
- a helical element is bi-directional, in that it extends first in one circumferential direction and then the other between the two locations and has a peak.
- a stent has a plurality of axially spaced strut portions defining generally tubular axial segments of the stent and constructed to be radially expandable.
- a helical portion is interposed axially between two strut portions, and the helical portion has a plurality of helical elements connected between circumferentially spaced locations on two strut portions.
- a helical element extends helically between these locations, and at least part of the helical portion has a greater diameter than a strut portion when the stent is in an expanded state.
- at least part of the helical portion has a smaller diameter than the strut portion when the strut is in an expanded state.
- the helical element is wound at least 90 degrees between strut elements connected to the helical element. In another embodiment, the helical element is wound at least 360 degrees between strut elements connected to the helical element.
- stent grafts are formed of a biocompatible graft material covering the outside, inside or both the outside and inside of the stent.
- the stent graft can have any embodiment of a stent structure of the present invention.
- Stent graft devices are used, for example, in the treatment of aneurysms, dissections and tracheo-bronchial strictures.
- the stent can also be coated with a polymer and/or drug eluting material as are known in the art.
- FIG. 1A is a plan view of a first embodiment of a stent in accordance with the present invention, the stent being shown in an unexpanded state;
- FIG. 1B is a plan view of the first embodiment of a stent in accordance with the present invention, the stent being shown in a radially expanded state;
- FIG. 2 is a plan view of a second embodiment of a stent in accordance with the present invention.
- FIG. 3 is a plan view of a third embodiment of a stent in accordance with the present invention.
- FIG. 4 is a plan view of a fourth embodiment of a stent in accordance with the present invention.
- FIG. 5 is a sectional end view of a fifth embodiment of a stent in accordance with the present invention.
- FIG. 6 is a lengthwise side outline view of the same embodiment as FIG. 5 ;
- FIG. 7A is a plan view of another embodiment of a stent in accordance with the present invention.
- FIG. 7B is a plan view of another embodiment of the stent in accordance with the present invention.
- FIG. 8 is a sectional end view of another embodiment of the stent in accordance with the present invention.
- FIG. 9 is a lengthwise side outline view of the embodiment shown in FIG. 8 ;
- FIG. 10A is a sectional end view of an alternate embodiment of a stent in accordance with the present invention including graft material covering an outer surface of the stent;
- FIG. 10B is a sectional end view of an alternate embodiment of a stent in accordance with the present invention including graft material covering an inner surface of the stent;
- FIG. 10C is a sectional end view of an alternate embodiment of a stent in accordance with the present invention including graft material covering an outer surface and an inner surface of the stent;
- FIG. 11A is a side view of an alternate embodiment of a stent in accordance with the present invention including graft material attached to the strut portion, the graft material covering the strut portion and the helical portion;
- FIG. 11B is a side view of an alternate embodiment of a stent in accordance with the present invention including a plurality of sections of biocompatible graft material wherein a gap is provided between each of the sections of graft material;
- FIG. 11C is a side view of an alternate embodiment of a stent in accordance with the present invention including a plurality of sections of a biocompatible graft material wherein the graft material of adjacent sections is overlapped;
- FIG. 11D is a side view of an alternate embodiment of a stent in accordance with the present invention including a biocompatible graft material, the graft material having a bulge at the helical portions;
- FIG. 11E is a side view of an alternate embodiment of a stent in accordance with the present invention including a biocompatible graft material, the graft material having a plurality of longitudinal openings over the helical portions;
- FIG. 11F is a side view of an alternate embodiment of a stent in accordance with the present invention the graft material having a bulge at the helical portions and the graft material having a plurality of longitudinal openings over the helical portions;
- FIG. 11G is a side view of an alternate embodiment of a stent in accordance with the present invention including a biocompatible graft material having a plurality of helical openings corresponding to a pitch of the helical elements;
- FIG. 11H is a side view of an alternate embodiment of a stent in accordance with the present invention including a plurality of sections of biocompatible graft material each of the sections being attached to either the strut portion or the helical portion wherein a gap is provided between each of the sections of graft material;
- FIG. 11J is a side view of an alternate embodiment of a stent in accordance with the present invention including a plurality of sections of biocompatible graft material, each of the sections being attached to either the strut portion or the helical portion wherein adjacent sections of graft material is overlapped;
- FIG. 12A is a plan view of an alternate embodiment of a stent in an expanded state
- FIG. 12B is a plan view of the stent of FIG. 12A in a crimped state such that the gap between helical elements is the same throughout the helical portions. Additionally, the length of the stent is the same in both the crimped and expanded state;
- FIG. 12C is a plan view of the stent of FIG. 12A in a crimped state such that the gap between helical elements changes throughout the helical portion. Additionally, the stent is longer in the crimped state than the expanded state;
- FIG. 13 is a plan view of an alternate embodiment of a stent in accordance with the present invention.
- FIGS. 1A and 1B are plan views of a first embodiment of stent 10 in accordance with the present invention shown in an unexpanded state and expanded state, respectively.
- the term “plan view” will be understood to describe an unwrapped plan view. This could be thought of as slicing open a tubular stent along a line parallel to its axis and laying it out flat. It should therefore be appreciated that, in the actual stent, the top edge of the FIG. 1A will be joined to the lower edge.
- Stent 10 is made from a common material for self expanding stents, such as Nitinol nickel-titanium alloy (Ni/Ti), as is well known in the art.
- Ni/Ti Nitinol nickel-titanium alloy
- the stent is laser cut from tubing, for example, with a diameter of about 5 mm ( FIG. 1A ). It is then expanded and set to a diameter of about 8 mm ( FIG. 1B ), and for pre-deployment it would be crimped to a diameter appropriate for the application, for example about 3 mm.
- the present invention is applicable to any type and size of stent.
- Stent 10 is generally made up of strut portion 12 and helical portion 14 with axially aligned strut portion 12 alternating with helical portion 14 .
- strut portion 12 is positioned at either end of stent 10 .
- Strut portion 12 being radially expandable upon deployment.
- Each strut portion 12 includes strut ring 16 having a pattern of wave-like strut elements 16 a that progresses circumferentially about the stent.
- Each strut element 16 a has a width equal to the peak to peak distance around the stent and a length equal to the peak-to-peak distance along the length of the stent. It will be appreciated that strut ring 16 could be partially straightened (stretched vertically in FIG.
- the material of which stent 10 is made is such that strut element 16 a will retain some wave-like shape in a radially expanded state.
- the stent would be crimped and fitted into a catheter, and it would expand after the catheter is inserted into the vessel and the stent is advanced out of the catheter.
- Each helical portion is made up of a plurality of side-by-side helical elements 18 , each of which is helically wound about an axis of stent 10 .
- Helical portion 14 is expandable radially upon deployment and compressible, expandable and bendable in a deployed state.
- Helical elements 18 can be connected between opposed individual wave portions of strut element 16 a of different strut portions 12 .
- each helical element 18 makes a complete rotation about the surface of stent 10 . However, they can make a partial rotation or more than one rotation.
- the helical portion is preferably constructed to permit repeated axial compression or expansion of about 20% (preferably between 15% and 25%) and simultaneously permit bending with a minimum bending radius of about 13 mm (preferably between 10 mm and 16 mm), all without failure.
- helical element 18 is wound at least 90 degrees between strut elements 16 a connected to helical elements 18 .
- helical element 18 is wound at least 360 degrees between strut elements 16 a connected to helical elements 18 .
- FIG. 2 is a plan view of a second embodiment of stent 20 similar to stent 10 of FIG. 1 .
- the primary differences are in the structure of strut portions 12 ′ and that there are right-handed and left-handed helical portions ( 14 R and 14 L, respectively).
- Each strut portion 12 ′ comprises two adjacent strut rings 26 , 27 connected by short link 28 .
- the closely opposed peaks of strut elements 26 a, 27 a are connected by short link 28 , so that each strut portion 12 ′ has a double strut ring structure.
- twin or multiple strut ring strut portions is that they offer increased radial stiffness over the single strut ring strut portion and can stabilize the strut portions so they are less affected by axial forces.
- a right-handed helical portion 14 R the elements 18 progress clockwise about the surface of stent 10 and, in a left-handed helical portion 14 L, they progress counterclockwise.
- Helical elements 18 essentially float and permit relatively large displacements about and along the stent axis between the two strut ring portions at either end.
- the diameter of the stent at each helical portion 14 R, 14 L is the same as the diameter of the stent at the strut portions 12 on either side. However, this need not be the case, as will become evident from additional embodiments discussed below.
- a benefit of using left-handed and right-handed helical portions is that when the stent deploys the two portions rotate in opposite directions, maintaining the relative rotational positions of different axial portions of the stent.
- FIG. 3 is another embodiment of stent 30 in accordance with the present invention. It is similar to stent 20 of FIG. 2 , except that helical portions 34 include helical element 38 which progresses bi-directionally (first counterclockwise and then clockwise) about the perimeter of stent 30 between connection locations on two different strut portions 12 ′. Helical element 38 is wound at least 90 degrees from a first strut portion 12 ′ to peak 35 and is wound 90 degrees from peak 35 to a second strut portion 12 ′ in order to maintain flexibility.
- the one-directional helical elements 18 of FIG. 1A and 1B can allow adjacent strut portions to rotate relative to one another.
- the bi-directional helical elements 38 limit the amount adjacent strut portions can rotate about the stent axis relative to one another but still provide axial and bending flexibility.
- FIG. 4 is a plan view of a fourth embodiment of a stent in accordance with the present invention.
- stent 40 has strut portions 12 ′ of FIG. 2 and the helical portions 14 L, 14 R ( FIG. 2 ) and helical portions 34 ( FIG. 3 ).
- the advantage of this construction is that combining different types of helical elements allows a mix of properties as described herein, providing the opportunity for further optimization of overall stent performance for a given application.
- FIG. 5 is a sectional view perpendicular to the axis of a fifth embodiment of stent 30 ′ in accordance with the present invention
- FIG. 6 is a side outline view of the same embodiment.
- the stent has the structure shown in FIG. 3 , except that helical portions 38 ′ have a larger diameter than strut portions 12 ′. In this construction the radial stiffness of the helical portions is increased, but to a lesser degree than the strut portions.
- the helical portions may not have as much outward force on a vessel as the strut portions when the strut is expanded.
- the geometry of FIG. 6 will tend to force the helical portions to expand more than the strut portions, increasing the outward force of the helical portions, which equalizes the radial stiffness.
- Nitinol structures have a biased stiffness, such that the force required to collapse the structure back towards the collapsed state is generally greater than the force that continues to dilate the diseased vessel when the stent is in its expanded state.
- a balloon is used to assist the expansion/dilation of the vessel.
- the biased stiffness is enough to support the open vessel, but the outward force may not be enough to open the vessel (or it may take a longer period of time).
- a stent with the type of geometry shown in FIG. 5 would therefore be a good expedient to use in conjunction with balloon assisted expansion, or other applications requiring additional expansive force.
- FIG. 7A is a plan view of another embodiment of stent 40 B′ in accordance with the present invention.
- Stent 40 B′ includes strut member 42 .
- Strut member 42 progresses helically from one end of stent 40 B′ to the other.
- Strut member 42 forms main body of stent 40 B′.
- each strut element 44 a is connected to a strut in a subsequent winding of strut member 42 by helical element 46 .
- helical element 46 of helical portion 45 progresses helically less than one full rotation of 360 degrees about stent 40 B′.
- Helical element 46 progresses in a direction opposite of the direction of which strut member 42 progresses helically about stent 40 B′.
- helical elements 46 are axially abutted, forming a type of spring which permits a great deal of flexibility and axial expansion, while strut member 42 provides radial strength and retains the stent in its expanded condition.
- FIG. 7B is a plan view of another embodiment of stent 40 C′ in accordance with the present invention.
- Stent 40 C′ is similar to stent 40 B′ and includes strut member 42 .
- Strut member 42 progresses helically from one end of stent 40 C′ to the other.
- Strut member 42 forms main body of stent 40 C′.
- each strut element 44 a is connected to a strut in a subsequent winding of strut member 42 by helical element 47 .
- helical element 47 progresses helically about stent 40 C′ in the same direction as strut member 42 progresses helically about stent 40 C′.
- Stent 40 C′ includes transitional helical portions 49 and strut portions 48 at either end of stent 40 C′ to allow strut portion 48 to be provided at either end of stent 40 C′.
- Strut portion 48 is wound about an axis of stent 40 C.
- Strut portion 48 has acute angle A 2 formed between a plane perpendicular to the axis of stent 40 C and a winding of strut portion 48 that is smaller than acute angle A 1 formed between the plane perpendicular to the axis of stent 40 C and the winding of strut member 42 .
- Transitional helical portion 49 interconnects about one rotational winding or less of strut portion 48 .
- Strut portion 48 is wound about an axis of stent 40 C′ having a number of windings less than about 1 ⁇ 4 of the total number of windings of strut member 42 .
- the number of helical elements strut elements 50 in one rotation of a winding of strut portion 48 is greater than the number of strut elements 44 a in one rotation of strut member 42 .
- Stents 40 B′ and 40 C′ have the advantage that the flexible helical elements are distributed more continuously along the length of the stent and may provide more continuous flexibility.
- stent 40 B′ or 40 C′ various modifications to stent 40 B′ or 40 C′ are possible, depending upon the requirements of a particular design. For example, it might be desirable to connect fewer than all of strut elements 44 a in a particular winding to a subsequent winding, reducing the number of helical elements 46 .
- Helical elements 46 can extend for less or for any integer or non-integer multiple of a rotation.
- a stent could also be made of a plurality of tubular sections each having the construction of stent 40 B′ or 40 C′ and joined lengthwise by another type of section.
- FIG. 8 is a sectional view perpendicular to the axis of an embodiment of stent 20 ′ in accordance with the present invention
- FIG. 9 is a side outline view of the same embodiment.
- the stent has the structure shown in FIG. 1A , except that helical portions 14 ′ neck down to a smaller diameter than strut portions 12 ′. In this construction the helical portions will exert less force on the vessel wall than if the helical portions were the same diameter. Reducing the force the stent exerts on a vessel wall can reduce the amount of damage done to a vessel and provide a better performing stent.
- FIGS. 10A-10C are sectional views perpendicular to the axis of the stent in accordance with the present invention.
- Stent graft 60 , 70 and 80 have a stent structure of the present invention of any of the embodiments described above with helical portions interposed between strut portions.
- biocompatible graft material 62 covers outside 64 of stent graft 60 , as shown in FIG. 10A .
- bio compatible graft material 62 covers inside 74 of stent 70 , as shown in FIG. 10B .
- graft material 62 covers outside 64 and inside 74 of stent 80 , as shown in FIG. 10C .
- Graft material 62 can be formed of any number of polymers or other biocompatible materials that have been woven or formed into a sheet or knitted surface. Alternatively, the stent can be coated with a polymer and/or drug eluting material as are known in the art.
- FIGS. 11A-11J are side profile views of stent grafts including the features of the flexible stent structure of the present invention.
- Stent graft 100 comprises a continuous covering of graft material 102 covering stent 10 , as shown in FIG. 11A .
- Graft material 102 is attached to strut portions 12 .
- Graft material 102 covers and is not attached to helical portions 14 .
- Stent graft 110 comprises a plurality of sections 111 of graft material 112 covering the stent structure, as shown in FIG. 11B .
- Graft material 112 is attached to strut portions 12 .
- Graft material 112 covers at least a portion of helical portions 14 and is not attached to helical portions 14 .
- Gap 115 is positioned between adjacent sections 111 of graft material 112 . Gap 115 will typically range in size between 0 (meaning no gap) and about 20% of the length of helical portion 14 .
- Stent graft 120 comprises a plurality of sections 121 of graft material 122 covering the stent structure, as shown in FIG. 11C .
- Graft material 122 is attached to strut portions 12 .
- Graft material 122 covers and is not attached to helical portions 14 .
- Sections 121 of graft material 122 are positioned such that there is an overlap 125 between adjacent sections 121 of graft material 122 .
- Overlap 125 will typically range in size between 0 (meaning no gap) and about 40% of the length of helical portion 14 .
- Stent graft 130 comprises a continuous covering of graft material 132 , as shown in FIG. 11D .
- Graft material 132 is attached to strut portions 12 .
- Graft material 132 covers and is not attached to helical portions 14 .
- Graft material 132 has bulge 133 at helical portions 14 .
- Stent graft 140 comprises a continuous covering of graft material 142 , as shown in FIG. 11E .
- Graft material 142 has a plurality of longitudinal openings 144 over helical portions 14 .
- Stent graft 150 comprises a continuous covering of graft material 152 , as shown in FIG. 11F .
- Graft material 152 has bulge 153 at helical portions 14 and has a plurality of longitudinal openings 154 over helical portions 14 .
- Stent graft 160 comprises a continuous covering of graft material 162 , as shown in FIG. 11F .
- Graft material 162 has helical openings 164 in helical portions 14 that correspond to the pitch and angle of helical portions 14 .
- Stent graft 170 comprises a plurality of sections 171 of graft material 172 covering stent 10 , as shown in FIG. 11H .
- Sections 171 can be attached to strut portions 12 or helical portions 14 .
- Gap 175 is positioned between adjacent sections 171 of graft material 172 .
- Gap 175 will typically range in size between 0 (meaning no gap) and about 20% of the length of helical portion 14 .
- Stent graft 180 comprises a plurality of sections 181 of graft material 182 covering stent 10 , as shown in FIG. 11J .
- Sections 181 can be attached to strut portions 12 or helical portions 14 .
- Sections 181 of graft material 182 are positioned such that there is an overlap 185 between adjacent sections 181 of graft material 182 .
- Overlap 185 will typically range in size between 0 (meaning no gap) and about 40% of the length of helical portion 14 .
- FIGS. 12A , 12 B and 12 C are plan views of stent 200 in accordance with the present invention.
- FIG. 12A shows stent 200 in an expanded state with gap 202 between helical elements 18 .
- FIGS. 12B and 12C show stent 200 in two different compressed states.
- stent 200 is compressed such that gap 212 between side-by-side helical elements 18 is about the same throughout helical portion 14 .
- the size of gap 212 between side-by-side helical elements 18 can range between 0 and about the size of the gap 202 in the expanded state, for example, as shown in FIG. 12A . In other words, when the size of the gap is 0, there is no space between side-by-side helical elements 18 and side-by-side helical elements 18 contact one another.
- the helical elements of the stent shown in FIG. 12B have been wrapped around the stent a number of times such that in the crimped state the overall length 211 of the stent in the crimped state is the same as the overall length 201 of the stent in the expanded state shown in FIG. 12A , thereby eliminating foreshortening.
- the spacing between windings of strut member 42 in the compressed state is substantially the same to the spacing between windings of strut member 12 in the deployed state.
- stent 200 is compressed such that helical element 18 is elongated and gap 222 between side-by-side helical elements 18 varies throughout the axial length of helical portion 14 .
- the size of gap 222 between adjacent helical elements 18 can range between 0 and about the size of the gap 202 in the expanded state, for example, as shown in FIG. 12A . In other words, when the size of the gap is 0, there is no space between side-by-side helical elements 18 and side-by-side helical elements 18 contact one another.
- Helical elements 18 are elongated elements without overlapping in the radial direction. In the deployed state, helical elements 18 are substantially parallel.
- Strut member 12 and helical elements 18 define a cylinder having a constant diameter.
- the overall length 221 of the stent in the crimped state is greater then the overall length 201 of the stent in the expanded state.
- helical elements 18 are elongated elements in both the compressed and deployed state wherein the distance between at least some adjacent helical elements in the compressed state varies along the length of the adjacent helical elements and is in a range from zero and about the maximum distance between adjacent helical elements in the deployed state.
- the spacing between windings of strut member 42 in the compressed state is greater than the spacing between windings of strut member 12 in the deployed state.
- Stent 200 in the compressed state as shown in FIG.
- the minimum angle of helical elements 18 with the longitudinal axis of stent 200 in the compressed state is less than the minimum angle of helical elements 18 with the longitudinal axis of stent 200 in the deployed state.
- An additional method can be provided to crimp the stent such that the length of helical portions is shorter in the crimped state than in the expanded state. For example, if the stent of FIG. 12A were crimped similar to that shown in FIG. 12B , except no gap exists between side-by-side helical elements the stent would be have length 211 in the crimped state which is shorter than length 201 in the expanded state.
- a method of crimping provides a stent where the overall length is the same in the crimped and expanded state and there is no gap between helical elements in the crimped state.
- one preferred embodiment of the stent is to permit repeated axial compression or expansion of about 20% and simultaneously permit bending with a minimum bending radius of about 13 mm.
- One method to construct a stent of the present invention with a specific target for flexibility is to vary the ratio between the sum of the gap space in the helical portion to the overall length. By increasing that ratio, the flexibility of the stent increases. This ratio will also be approximately the maximum axial compression the stent will allow. It will be appreciated that the maximum axial compression for safety may be limited by other factors such as strain in the helical elements.
- FIG. 13 is a plan view of a stent 300 in accordance with the present invention.
- Stent 300 is similar to other embodiments described above except it includes various configurations and various axial lengths of strut portions and various configurations and various axial lengths of helical portions.
- Strut portions 302 positioned at the outer most portion of stent 300 includes long strut elements 301 .
- Long strut elements 301 have length 311 .
- Length 311 of long strut element 301 is greater than length 312 of strut portions 304 positioned at the inner portion of stent 300 .
- Long strut elements 301 provided on the ends of the stent may be advantageous to provide better anchoring and provide an area for adjacent stents to overlap, but not impede the flexibility of the helical portion.
- the length of diseased artery may be long, often longer than 10 cm. Multiple stents may be required to treat these long sections of diseased arteries.
- a common procedure in this case is to overlap the adjacent stents so that the vessel being treated is covered.
- An advantage of the present invention is that the elements that allow bending and axial flexibility (helical portion) are different than the elements that provide radial structure (strut portion) so that the strut portions on adjacent stents may overlap and not impede the movement of the helical portion and therefore the overall flexibility of the stent.
- Helical portion 303 that is adjacent to the strut portion 302 comprises helical elements 18 that are connected to every strut element 301 of strut portion 302 .
- Helical portion 303 can provide a high percentage of surface area for optimized delivery of a drug or other therapeutic agent.
- Strut portion 304 is connected to helical portion 303 by helical element 18 at every strut element 16 a on side 320 of strut portion 304 and is connected to helical portion 309 at every other strut element 16 a on side 321 of strut portion 304 .
- Helical portion 309 provides a lower percentage of surface area and greater flexibility than helical portion 303 . This type of configuration can provide a transition from a stiffer helical portion that has a high percentage of surface area to a more flexible helical portion.
- Helical portion 309 has a higher ratio of the sum of gap lengths 323 to length 324 of helical portion 309 than the sum of gap lengths 325 to length 326 of helical portion 303 , so that helical portion 309 will generally have greater flexibility.
- Strut portion 306 has half as many strut elements 305 as strut portions 302 or 304 and therefore generally has more open area compared to strut portion 302 or strut portion 304 .
- An advantage of a stent including a portion having a larger open area than other portions of the stent is that the larger open portion of the stent can be placed over an arterial bifurcation and not impede blood flow. Whereas the strut portion with a higher strut element density may impede blood flow.
- the stent structure of the present invention namely flexible helical portions flanked on either side by strut portions, provide an optimized structure where the strut portions stabilize a naturally unstable helical structure, and the helical portions provide net flexibility. There is substantial design optimization potential in combining various embodiments of the two portions.
- the flexible stents and stent grafts of the present invention may be placed within vessels using procedures well known in the art.
- the flexible stents and stent grafts may be loaded into the proximal end of a catheter and advanced through the catheter and released at the desired site.
- the flexible stents and stent grafts may be carried about the distal end of the catheter in a compressed state and released at the desired site.
- the flexible stents or stent grafts may either be self-expanding or expanded by means such as an inflatable balloon segment of the catheter. After the stent(s) or stent graft(s) have been deposited at the desired intralumenal site, the catheter is withdrawn.
- the flexible stents and stent grafts of the present invention may be placed within body lumen such as vascular vessels or ducts of any mammal species including humans, without damaging the lumenal wall.
- the flexible stent can be placed within a lesion or an aneurysm for treating the aneurysm.
- the flexible stent is placed in a super femoral artery upon insertion into the vessel, the flexible stent or stent grafts provides coverage of at least about 50% of the vessel.
- a stent could be made with only right-handed or only left-handed helical portions, or the helical portions could have multiple reversals in winding direction rather than just one.
- the helical portions could have any number of turns per unit length or a variable pitch, and the strut rings and/or helical portions could be of unequal length along the stent.
Abstract
A flexible stent structure includes a plurality of axially spaced strut portions defining generally tubular axial segments of the stent and constructed to be radially expandable. A helical portion is interposed axially between two strut portions and has a plurality of helical elements connected between circumferentially spaced locations on the two strut portions. The helical elements extend helically between those locations and the length of a helical element is sufficient so that, when the stent is in a radially expanded state, it can simultaneously withstand repeated axial compression or expansion and bending.
Description
- This application is a divisional of U.S. patent application Ser. No. 11/397,987, filed Apr. 4, 2006, which is a continuation-in-part of U.S. patent application Ser. No. 11/250,226 filed Oct. 14, 2005, now abandoned, which claims the benefit of U.S. Provisional patent application No. 60/667,613 filed Apr. 4, 2005, the entirety of all of which are hereby incorporated by reference into this application.
- The present invention relates generally to expandable tubular structures capable of insertion into small spaces in living bodies and, more particularly, concerns a stent structure which is capable of substantial and repeated flexing at points along its length without mechanical failures and with no substantial changes in its geometry.
- A stent is a tubular structure that, in a radially compressed or crimped state, may be inserted into a confined space in a living body, such as an artery or other vessel. After insertion, the stent may be expanded radially to enlarge the space in which it is located. Stents are typically characterized as balloon-expanding (BX) or self-expanding (SX). A balloon-expanding stent requires a balloon, which is usually part of a delivery system, to expand the stent from within and to dilate the vessel. A self expanding stent is designed, through choice of material, geometry, or manufacturing techniques, to expand from the crimped state to an expanded state once it is released into the intended vessel. In certain situations higher forces than the expanding force of the self expanding stent are required to dilate a diseased vessel. In this case, a balloon or similar device might be employed to aid the expansion of a self expanding stent.
- Stents are typically used in the treatment of vascular and non-vascular diseases. For instance, a crimped stent may be inserted into a clogged artery and then expanded to restore blood flow in the artery. Prior to release, the stent would typically be retained in its crimped state within a catheter and the like. Upon completion of the procedure, the stent is left inside the patient's artery in its expanded state. The health, and sometimes the life, of the patient depend upon the stent's ability to remain in its expanded state.
- Many available stents are flexible in their crimped state in order to facilitate the delivery of the stent, for example within an artery. Few are flexible after being deployed and expanded. Yet, after deployment, in certain applications, a stent may be subjected to substantial flexing or bending, axial compressions and repeated displacements at points along its length, for example, when stenting the superficial femoral artery. This can produce severe strain and fatigue, resulting in failure of the stent.
- A similar problem exists with respect to stent-like structures. An example would be a stent-like structure used with other components in a catheter-based valve delivery system. Such a stent-like structure holds a valve which is placed in a vessel.
- In accordance with the present invention, a stent or a stent-like structure is constructed to have different types of tubular portions along its length. In general, there are strut portions and helical portions, where the strut portions are constructed primarily to provide radial expansion and radial strength, and the helical portions are constructed primarily to permit repeated flexing and axial compression and expansion. The flexing and axial compression are likely to be required simultaneously, so the stent structure permits repeated and substantial flexing while in an axially compressed or expanded state, and it permits axial compression while in a flexed state. Preferably, strut portions are provided between helical portions or helical portions are provided between strut portions. In a preferred embodiment, the stent is self-expanding and strut portions and helical portions alternate along the length of the stent.
- The stent is preferably constructed so that, in the expanded state the helical portions permit axial compression or expansion of about 20% (preferably between 15% and 25%) and simultaneously permit bending with a minimum bending radius of about 13 mm (preferably between 10 mm and 16 mm).
- In accordance with another aspect of the invention, a helical portion is made of helical elements which extend helically about the axis of the stent between points on two different strut portions which are spaced apart circumferentially by a distance which is more than approximately 25% of the circumference of the stent (which is equivalent to an extent of 90 degrees about the axis of the stent) when it is in its expanded state.
- In accordance with yet another aspect of the invention, a helical portion is made of helical elements which extend helically about the axis of the stent between locations on two different strut portions. In one embodiment a helical element is bi-directional, in that it extends first in one circumferential direction and then the other between the two locations and has a peak.
- In accordance with yet another aspect of the invention, a stent has a plurality of axially spaced strut portions defining generally tubular axial segments of the stent and constructed to be radially expandable. A helical portion is interposed axially between two strut portions, and the helical portion has a plurality of helical elements connected between circumferentially spaced locations on two strut portions. A helical element extends helically between these locations, and at least part of the helical portion has a greater diameter than a strut portion when the stent is in an expanded state. In an alternate embodiment, at least part of the helical portion has a smaller diameter than the strut portion when the strut is in an expanded state.
- In one embodiment, the helical element is wound at least 90 degrees between strut elements connected to the helical element. In another embodiment, the helical element is wound at least 360 degrees between strut elements connected to the helical element.
- In an alternate embodiment, stent grafts are formed of a biocompatible graft material covering the outside, inside or both the outside and inside of the stent. The stent graft can have any embodiment of a stent structure of the present invention. Stent graft devices are used, for example, in the treatment of aneurysms, dissections and tracheo-bronchial strictures. The stent can also be coated with a polymer and/or drug eluting material as are known in the art.
- The foregoing description, as well as further objects, features, and advantages of the present invention will be understood more completely from the following detailed description of presently preferred, but nonetheless illustrative embodiments in accordance with the present invention, with reference being had to the accompanying drawings, in which:
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FIG. 1A is a plan view of a first embodiment of a stent in accordance with the present invention, the stent being shown in an unexpanded state; -
FIG. 1B is a plan view of the first embodiment of a stent in accordance with the present invention, the stent being shown in a radially expanded state; -
FIG. 2 is a plan view of a second embodiment of a stent in accordance with the present invention; -
FIG. 3 is a plan view of a third embodiment of a stent in accordance with the present invention; -
FIG. 4 is a plan view of a fourth embodiment of a stent in accordance with the present invention; -
FIG. 5 is a sectional end view of a fifth embodiment of a stent in accordance with the present invention; -
FIG. 6 is a lengthwise side outline view of the same embodiment asFIG. 5 ; -
FIG. 7A is a plan view of another embodiment of a stent in accordance with the present invention; -
FIG. 7B is a plan view of another embodiment of the stent in accordance with the present invention; -
FIG. 8 is a sectional end view of another embodiment of the stent in accordance with the present invention; -
FIG. 9 is a lengthwise side outline view of the embodiment shown inFIG. 8 ; -
FIG. 10A is a sectional end view of an alternate embodiment of a stent in accordance with the present invention including graft material covering an outer surface of the stent; -
FIG. 10B is a sectional end view of an alternate embodiment of a stent in accordance with the present invention including graft material covering an inner surface of the stent; -
FIG. 10C is a sectional end view of an alternate embodiment of a stent in accordance with the present invention including graft material covering an outer surface and an inner surface of the stent; -
FIG. 11A is a side view of an alternate embodiment of a stent in accordance with the present invention including graft material attached to the strut portion, the graft material covering the strut portion and the helical portion; -
FIG. 11B is a side view of an alternate embodiment of a stent in accordance with the present invention including a plurality of sections of biocompatible graft material wherein a gap is provided between each of the sections of graft material; -
FIG. 11C is a side view of an alternate embodiment of a stent in accordance with the present invention including a plurality of sections of a biocompatible graft material wherein the graft material of adjacent sections is overlapped; -
FIG. 11D is a side view of an alternate embodiment of a stent in accordance with the present invention including a biocompatible graft material, the graft material having a bulge at the helical portions; -
FIG. 11E is a side view of an alternate embodiment of a stent in accordance with the present invention including a biocompatible graft material, the graft material having a plurality of longitudinal openings over the helical portions; -
FIG. 11F is a side view of an alternate embodiment of a stent in accordance with the present invention the graft material having a bulge at the helical portions and the graft material having a plurality of longitudinal openings over the helical portions; -
FIG. 11G is a side view of an alternate embodiment of a stent in accordance with the present invention including a biocompatible graft material having a plurality of helical openings corresponding to a pitch of the helical elements; -
FIG. 11H is a side view of an alternate embodiment of a stent in accordance with the present invention including a plurality of sections of biocompatible graft material each of the sections being attached to either the strut portion or the helical portion wherein a gap is provided between each of the sections of graft material; -
FIG. 11J is a side view of an alternate embodiment of a stent in accordance with the present invention including a plurality of sections of biocompatible graft material, each of the sections being attached to either the strut portion or the helical portion wherein adjacent sections of graft material is overlapped; -
FIG. 12A is a plan view of an alternate embodiment of a stent in an expanded state; -
FIG. 12B is a plan view of the stent ofFIG. 12A in a crimped state such that the gap between helical elements is the same throughout the helical portions. Additionally, the length of the stent is the same in both the crimped and expanded state; -
FIG. 12C is a plan view of the stent ofFIG. 12A in a crimped state such that the gap between helical elements changes throughout the helical portion. Additionally, the stent is longer in the crimped state than the expanded state; and -
FIG. 13 is a plan view of an alternate embodiment of a stent in accordance with the present invention. - Reference will now be made in greater detail to a preferred embodiment of the invention, an example of which is illustrated in the accompanying drawings. Wherever possible, the same reference numerals will be used throughout the drawings and the description to refer to the same or like parts.
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FIGS. 1A and 1B are plan views of a first embodiment ofstent 10 in accordance with the present invention shown in an unexpanded state and expanded state, respectively. As used herein, the term “plan view” will be understood to describe an unwrapped plan view. This could be thought of as slicing open a tubular stent along a line parallel to its axis and laying it out flat. It should therefore be appreciated that, in the actual stent, the top edge of theFIG. 1A will be joined to the lower edge. -
Stent 10 is made from a common material for self expanding stents, such as Nitinol nickel-titanium alloy (Ni/Ti), as is well known in the art. Typically, the stent is laser cut from tubing, for example, with a diameter of about 5 mm (FIG. 1A ). It is then expanded and set to a diameter of about 8 mm (FIG. 1B ), and for pre-deployment it would be crimped to a diameter appropriate for the application, for example about 3 mm. However, it is contemplated that the present invention is applicable to any type and size of stent. -
Stent 10 is generally made up ofstrut portion 12 andhelical portion 14 with axially alignedstrut portion 12 alternating withhelical portion 14. In a preferred embodiment,strut portion 12 is positioned at either end ofstent 10.Strut portion 12 being radially expandable upon deployment. Eachstrut portion 12 includesstrut ring 16 having a pattern of wave-like strut elements 16 a that progresses circumferentially about the stent. Eachstrut element 16 a has a width equal to the peak to peak distance around the stent and a length equal to the peak-to-peak distance along the length of the stent. It will be appreciated thatstrut ring 16 could be partially straightened (stretched vertically inFIG. 1B ) so as to widenstrut elements 16 a and reduce their length. This is equivalent to expandingstent 10 radially. Preferably, the material of whichstent 10 is made is such thatstrut element 16 a will retain some wave-like shape in a radially expanded state. For delivery, the stent would be crimped and fitted into a catheter, and it would expand after the catheter is inserted into the vessel and the stent is advanced out of the catheter. - Each helical portion is made up of a plurality of side-by-side
helical elements 18, each of which is helically wound about an axis ofstent 10.Helical portion 14 is expandable radially upon deployment and compressible, expandable and bendable in a deployed state.Helical elements 18 can be connected between opposed individual wave portions ofstrut element 16 a ofdifferent strut portions 12. In this embodiment, eachhelical element 18 makes a complete rotation about the surface ofstent 10. However, they can make a partial rotation or more than one rotation. The helical portion is preferably constructed to permit repeated axial compression or expansion of about 20% (preferably between 15% and 25%) and simultaneously permit bending with a minimum bending radius of about 13 mm (preferably between 10 mm and 16 mm), all without failure. - Improved flexibility and axial compression can generally be accomplished if
helical element 18 is wound at least 90 degrees betweenstrut elements 16 a connected tohelical elements 18. Alternatively,helical element 18 is wound at least 360 degrees betweenstrut elements 16 a connected tohelical elements 18. -
FIG. 2 is a plan view of a second embodiment ofstent 20 similar tostent 10 ofFIG. 1 . The primary differences are in the structure ofstrut portions 12′ and that there are right-handed and left-handed helical portions (14R and 14L, respectively). Eachstrut portion 12′ comprises two adjacent strut rings 26, 27 connected byshort link 28. The closely opposed peaks ofstrut elements short link 28, so that eachstrut portion 12′ has a double strut ring structure. It would also be possible to connect multiple strut rings together to form a larger strut portion. The advantage of twin or multiple strut ring strut portions is that they offer increased radial stiffness over the single strut ring strut portion and can stabilize the strut portions so they are less affected by axial forces. - In a right-handed
helical portion 14R, theelements 18 progress clockwise about the surface ofstent 10 and, in a left-handedhelical portion 14L, they progress counterclockwise.Helical elements 18 essentially float and permit relatively large displacements about and along the stent axis between the two strut ring portions at either end. In this embodiment, it will be appreciated that the diameter of the stent at eachhelical portion strut portions 12 on either side. However, this need not be the case, as will become evident from additional embodiments discussed below. A benefit of using left-handed and right-handed helical portions is that when the stent deploys the two portions rotate in opposite directions, maintaining the relative rotational positions of different axial portions of the stent. -
FIG. 3 is another embodiment ofstent 30 in accordance with the present invention. It is similar tostent 20 ofFIG. 2 , except thathelical portions 34 includehelical element 38 which progresses bi-directionally (first counterclockwise and then clockwise) about the perimeter ofstent 30 between connection locations on twodifferent strut portions 12′.Helical element 38 is wound at least 90 degrees from afirst strut portion 12′ to peak 35 and is wound 90 degrees frompeak 35 to asecond strut portion 12′ in order to maintain flexibility. The one-directionalhelical elements 18 ofFIG. 1A and 1B can allow adjacent strut portions to rotate relative to one another. The bi-directionalhelical elements 38 limit the amount adjacent strut portions can rotate about the stent axis relative to one another but still provide axial and bending flexibility. -
FIG. 4 is a plan view of a fourth embodiment of a stent in accordance with the present invention. In this case,stent 40 hasstrut portions 12′ ofFIG. 2 and thehelical portions FIG. 2 ) and helical portions 34 (FIG. 3 ). The advantage of this construction is that combining different types of helical elements allows a mix of properties as described herein, providing the opportunity for further optimization of overall stent performance for a given application. -
FIG. 5 is a sectional view perpendicular to the axis of a fifth embodiment ofstent 30′ in accordance with the present invention, andFIG. 6 is a side outline view of the same embodiment. The stent has the structure shown inFIG. 3 , except thathelical portions 38′ have a larger diameter thanstrut portions 12′. In this construction the radial stiffness of the helical portions is increased, but to a lesser degree than the strut portions. - When all portions of the stent have the same diameter, the helical portions may not have as much outward force on a vessel as the strut portions when the strut is expanded. The geometry of
FIG. 6 will tend to force the helical portions to expand more than the strut portions, increasing the outward force of the helical portions, which equalizes the radial stiffness. - Nitinol structures have a biased stiffness, such that the force required to collapse the structure back towards the collapsed state is generally greater than the force that continues to dilate the diseased vessel when the stent is in its expanded state. With some self expanding Nitinol stents, a balloon is used to assist the expansion/dilation of the vessel. The biased stiffness is enough to support the open vessel, but the outward force may not be enough to open the vessel (or it may take a longer period of time). A stent with the type of geometry shown in
FIG. 5 would therefore be a good expedient to use in conjunction with balloon assisted expansion, or other applications requiring additional expansive force. -
FIG. 7A is a plan view of another embodiment ofstent 40B′ in accordance with the present invention.Stent 40B′ includesstrut member 42.Strut member 42 progresses helically from one end ofstent 40B′ to the other.Strut member 42 forms main body ofstent 40B′. In this embodiment, eachstrut element 44 a is connected to a strut in a subsequent winding ofstrut member 42 byhelical element 46. In this embodiment,helical element 46 ofhelical portion 45 progresses helically less than one full rotation of 360 degrees aboutstent 40B′.Helical element 46 progresses in a direction opposite of the direction of which strutmember 42 progresses helically aboutstent 40B′. - Preferably,
helical elements 46 are axially abutted, forming a type of spring which permits a great deal of flexibility and axial expansion, whilestrut member 42 provides radial strength and retains the stent in its expanded condition. -
FIG. 7B is a plan view of another embodiment of stent 40C′ in accordance with the present invention. Stent 40C′ is similar tostent 40B′ and includesstrut member 42.Strut member 42 progresses helically from one end of stent 40C′ to the other.Strut member 42 forms main body of stent 40C′. In the present embodiment, eachstrut element 44 a is connected to a strut in a subsequent winding ofstrut member 42 by helical element 47. In this embodiment, helical element 47 progresses helically about stent 40C′ in the same direction asstrut member 42 progresses helically about stent 40C′. Stent 40C′ includes transitional helical portions 49 and strut portions 48 at either end of stent 40C′ to allow strut portion 48 to be provided at either end of stent 40C′. Strut portion 48 is wound about an axis of stent 40C. Strut portion 48 has acute angle A2 formed between a plane perpendicular to the axis of stent 40C and a winding of strut portion 48 that is smaller than acute angle A1 formed between the plane perpendicular to the axis of stent 40C and the winding ofstrut member 42. Transitional helical portion 49 interconnects about one rotational winding or less of strut portion 48. Strut portion 48 is wound about an axis of stent 40C′ having a number of windings less than about ¼ of the total number of windings ofstrut member 42. The number of helical elements strut elements 50 in one rotation of a winding of strut portion 48 is greater than the number ofstrut elements 44 a in one rotation ofstrut member 42. -
Stents 40B′ and 40C′ have the advantage that the flexible helical elements are distributed more continuously along the length of the stent and may provide more continuous flexibility. Those skilled in the art will appreciate that various modifications tostent 40B′ or 40C′ are possible, depending upon the requirements of a particular design. For example, it might be desirable to connect fewer than all ofstrut elements 44 a in a particular winding to a subsequent winding, reducing the number ofhelical elements 46.Helical elements 46 can extend for less or for any integer or non-integer multiple of a rotation. A stent could also be made of a plurality of tubular sections each having the construction ofstent 40B′ or 40C′ and joined lengthwise by another type of section. -
FIG. 8 is a sectional view perpendicular to the axis of an embodiment ofstent 20′ in accordance with the present invention, andFIG. 9 is a side outline view of the same embodiment. The stent has the structure shown inFIG. 1A , except thathelical portions 14′ neck down to a smaller diameter thanstrut portions 12′. In this construction the helical portions will exert less force on the vessel wall than if the helical portions were the same diameter. Reducing the force the stent exerts on a vessel wall can reduce the amount of damage done to a vessel and provide a better performing stent. -
FIGS. 10A-10C are sectional views perpendicular to the axis of the stent in accordance with the present invention.Stent graft biocompatible graft material 62 covers outside 64 ofstent graft 60, as shown inFIG. 10A . Alternatively, biocompatible graft material 62 covers inside 74 ofstent 70, as shown inFIG. 10B . Alternatively,graft material 62 covers outside 64 and inside 74 ofstent 80, as shown inFIG. 10C .Graft material 62 can be formed of any number of polymers or other biocompatible materials that have been woven or formed into a sheet or knitted surface. Alternatively, the stent can be coated with a polymer and/or drug eluting material as are known in the art. -
FIGS. 11A-11J are side profile views of stent grafts including the features of the flexible stent structure of the present invention. -
Stent graft 100 comprises a continuous covering ofgraft material 102 coveringstent 10, as shown inFIG. 11A .Graft material 102 is attached to strutportions 12.Graft material 102 covers and is not attached tohelical portions 14. -
Stent graft 110 comprises a plurality ofsections 111 ofgraft material 112 covering the stent structure, as shown inFIG. 11B .Graft material 112 is attached to strutportions 12.Graft material 112 covers at least a portion ofhelical portions 14 and is not attached tohelical portions 14.Gap 115 is positioned betweenadjacent sections 111 ofgraft material 112.Gap 115 will typically range in size between 0 (meaning no gap) and about 20% of the length ofhelical portion 14. -
Stent graft 120 comprises a plurality ofsections 121 ofgraft material 122 covering the stent structure, as shown inFIG. 11C .Graft material 122 is attached to strutportions 12.Graft material 122 covers and is not attached tohelical portions 14.Sections 121 ofgraft material 122 are positioned such that there is anoverlap 125 betweenadjacent sections 121 ofgraft material 122. Overlap 125 will typically range in size between 0 (meaning no gap) and about 40% of the length ofhelical portion 14. -
Stent graft 130 comprises a continuous covering ofgraft material 132, as shown inFIG. 11D .Graft material 132 is attached to strutportions 12.Graft material 132 covers and is not attached tohelical portions 14.Graft material 132 hasbulge 133 athelical portions 14. -
Stent graft 140 comprises a continuous covering ofgraft material 142, as shown inFIG. 11E .Graft material 142 has a plurality oflongitudinal openings 144 overhelical portions 14. -
Stent graft 150 comprises a continuous covering ofgraft material 152, as shown inFIG. 11F .Graft material 152 hasbulge 153 athelical portions 14 and has a plurality oflongitudinal openings 154 overhelical portions 14. -
Stent graft 160 comprises a continuous covering ofgraft material 162, as shown inFIG. 11F .Graft material 162 hashelical openings 164 inhelical portions 14 that correspond to the pitch and angle ofhelical portions 14. -
Stent graft 170 comprises a plurality ofsections 171 ofgraft material 172 coveringstent 10, as shown inFIG. 11H .Sections 171 can be attached to strutportions 12 orhelical portions 14.Gap 175 is positioned betweenadjacent sections 171 ofgraft material 172.Gap 175 will typically range in size between 0 (meaning no gap) and about 20% of the length ofhelical portion 14. -
Stent graft 180 comprises a plurality ofsections 181 ofgraft material 182 coveringstent 10, as shown inFIG. 11J .Sections 181 can be attached to strutportions 12 orhelical portions 14.Sections 181 ofgraft material 182 are positioned such that there is anoverlap 185 betweenadjacent sections 181 ofgraft material 182. Overlap 185 will typically range in size between 0 (meaning no gap) and about 40% of the length ofhelical portion 14. -
FIGS. 12A , 12B and 12C are plan views ofstent 200 in accordance with the present invention.FIG. 12A showsstent 200 in an expanded state withgap 202 betweenhelical elements 18.FIGS. 12B and 12C showstent 200 in two different compressed states. InFIG. 12B stent 200 is compressed such thatgap 212 between side-by-sidehelical elements 18 is about the same throughouthelical portion 14. The size ofgap 212 between side-by-sidehelical elements 18 can range between 0 and about the size of thegap 202 in the expanded state, for example, as shown inFIG. 12A . In other words, when the size of the gap is 0, there is no space between side-by-sidehelical elements 18 and side-by-sidehelical elements 18 contact one another. - The helical elements of the stent shown in
FIG. 12B have been wrapped around the stent a number of times such that in the crimped state theoverall length 211 of the stent in the crimped state is the same as theoverall length 201 of the stent in the expanded state shown inFIG. 12A , thereby eliminating foreshortening. The spacing between windings ofstrut member 42 in the compressed state is substantially the same to the spacing between windings ofstrut member 12 in the deployed state. - In
FIG. 12C stent 200 is compressed such thathelical element 18 is elongated andgap 222 between side-by-sidehelical elements 18 varies throughout the axial length ofhelical portion 14. The size ofgap 222 between adjacenthelical elements 18 can range between 0 and about the size of thegap 202 in the expanded state, for example, as shown inFIG. 12A . In other words, when the size of the gap is 0, there is no space between side-by-sidehelical elements 18 and side-by-sidehelical elements 18 contact one another.Helical elements 18 are elongated elements without overlapping in the radial direction. In the deployed state,helical elements 18 are substantially parallel.Strut member 12 andhelical elements 18 define a cylinder having a constant diameter. InFIG. 12C , theoverall length 221 of the stent in the crimped state is greater then theoverall length 201 of the stent in the expanded state. In other words,helical elements 18 are elongated elements in both the compressed and deployed state wherein the distance between at least some adjacent helical elements in the compressed state varies along the length of the adjacent helical elements and is in a range from zero and about the maximum distance between adjacent helical elements in the deployed state. The spacing between windings ofstrut member 42 in the compressed state is greater than the spacing between windings ofstrut member 12 in the deployed state.Stent 200 in the compressed state, as shown inFIG. 12C , is longer than in the deployed state, as shown inFIG. 12A . The minimum angle ofhelical elements 18 with the longitudinal axis ofstent 200 in the compressed state is less than the minimum angle ofhelical elements 18 with the longitudinal axis ofstent 200 in the deployed state. - An additional method can be provided to crimp the stent such that the length of helical portions is shorter in the crimped state than in the expanded state. For example, if the stent of
FIG. 12A were crimped similar to that shown inFIG. 12B , except no gap exists between side-by-side helical elements the stent would be havelength 211 in the crimped state which is shorter thanlength 201 in the expanded state. In one embodiment, a method of crimping provides a stent where the overall length is the same in the crimped and expanded state and there is no gap between helical elements in the crimped state. - As described above, one preferred embodiment of the stent is to permit repeated axial compression or expansion of about 20% and simultaneously permit bending with a minimum bending radius of about 13 mm. One method to construct a stent of the present invention with a specific target for flexibility is to vary the ratio between the sum of the gap space in the helical portion to the overall length. By increasing that ratio, the flexibility of the stent increases. This ratio will also be approximately the maximum axial compression the stent will allow. It will be appreciated that the maximum axial compression for safety may be limited by other factors such as strain in the helical elements.
-
FIG. 13 is a plan view of astent 300 in accordance with the present invention.Stent 300 is similar to other embodiments described above except it includes various configurations and various axial lengths of strut portions and various configurations and various axial lengths of helical portions.Strut portions 302 positioned at the outer most portion ofstent 300 includeslong strut elements 301. Long strutelements 301 havelength 311.Length 311 oflong strut element 301 is greater thanlength 312 ofstrut portions 304 positioned at the inner portion ofstent 300. Long strutelements 301 provided on the ends of the stent may be advantageous to provide better anchoring and provide an area for adjacent stents to overlap, but not impede the flexibility of the helical portion. In some vasculatures, notably the femoropopliteal arteries, the length of diseased artery may be long, often longer than 10 cm. Multiple stents may be required to treat these long sections of diseased arteries. A common procedure in this case is to overlap the adjacent stents so that the vessel being treated is covered. When some conventional stents are overlapped in this manner, the mechanism which makes them flexible is impeded and this artificial stiffening can cause many problems, including stent fractures. An advantage of the present invention is that the elements that allow bending and axial flexibility (helical portion) are different than the elements that provide radial structure (strut portion) so that the strut portions on adjacent stents may overlap and not impede the movement of the helical portion and therefore the overall flexibility of the stent. -
Helical portion 303 that is adjacent to thestrut portion 302 compriseshelical elements 18 that are connected to everystrut element 301 ofstrut portion 302.Helical portion 303 can provide a high percentage of surface area for optimized delivery of a drug or other therapeutic agent.Strut portion 304 is connected tohelical portion 303 byhelical element 18 at everystrut element 16 a onside 320 ofstrut portion 304 and is connected tohelical portion 309 at everyother strut element 16 a onside 321 ofstrut portion 304.Helical portion 309 provides a lower percentage of surface area and greater flexibility thanhelical portion 303. This type of configuration can provide a transition from a stiffer helical portion that has a high percentage of surface area to a more flexible helical portion. -
Helical portion 309 has a higher ratio of the sum ofgap lengths 323 tolength 324 ofhelical portion 309 than the sum ofgap lengths 325 tolength 326 ofhelical portion 303, so thathelical portion 309 will generally have greater flexibility. -
Strut portion 306 has half asmany strut elements 305 asstrut portions portion 302 orstrut portion 304. An advantage of a stent including a portion having a larger open area than other portions of the stent is that the larger open portion of the stent can be placed over an arterial bifurcation and not impede blood flow. Whereas the strut portion with a higher strut element density may impede blood flow. - The stent structure of the present invention, namely flexible helical portions flanked on either side by strut portions, provide an optimized structure where the strut portions stabilize a naturally unstable helical structure, and the helical portions provide net flexibility. There is substantial design optimization potential in combining various embodiments of the two portions.
- The flexible stents and stent grafts of the present invention may be placed within vessels using procedures well known in the art. The flexible stents and stent grafts may be loaded into the proximal end of a catheter and advanced through the catheter and released at the desired site. Alternatively, the flexible stents and stent grafts may be carried about the distal end of the catheter in a compressed state and released at the desired site. The flexible stents or stent grafts may either be self-expanding or expanded by means such as an inflatable balloon segment of the catheter. After the stent(s) or stent graft(s) have been deposited at the desired intralumenal site, the catheter is withdrawn.
- The flexible stents and stent grafts of the present invention may be placed within body lumen such as vascular vessels or ducts of any mammal species including humans, without damaging the lumenal wall. For example, the flexible stent can be placed within a lesion or an aneurysm for treating the aneurysm. In one embodiment, the flexible stent is placed in a super femoral artery upon insertion into the vessel, the flexible stent or stent grafts provides coverage of at least about 50% of the vessel.
- Although presently preferred embodiments of the present invention have been disclosed for illustrative purposes, those skilled in the art will appreciate that many additions, modifications, and substitutions are possible without departing from the scope and spirit of the invention as defined by the accompanying claims. For example, a stent could be made with only right-handed or only left-handed helical portions, or the helical portions could have multiple reversals in winding direction rather than just one. Also, the helical portions could have any number of turns per unit length or a variable pitch, and the strut rings and/or helical portions could be of unequal length along the stent.
Claims (72)
1. Flexible stent comprising:
a helical portion comprising a plurality of side-by-side, individual helical elements helically wound about an axis of said stent, said helical portion being expandable radially upon deployment and compressible, expandable and bendable in a deployed state; and a strut portion on either side of said helical portion, each of said strut portions comprising axially aligned strut elements having a first end connected to said helical elements of said helical portion, said strut portions being radially expandable upon deployment.
2. The stent of claim 1 wherein said helical elements are wound at least 90 degrees between said strut elements connected to said helical elements in said deployed state.
3. The stent of claim 1 wherein said helical elements are wound at least 360 degrees between said strut elements connected to said helical elements in said deployed state.
4. The stent of claim 1 further comprising one or more additional said helical portions and one or more additional said strut portions wherein one of said one or more additional said helical portions is connected to a second end of one of said strut portions, said one or more additional said helical portions being connected respectively to said one or more additional said strut portions such that each of said helical portions is interposed between a pair of said strut portions.
5. The stent of claim 4 wherein said helical elements of each of said helical portions are wound in the same direction.
6. The stent of claim 4 wherein said helical elements of at least one of said helical portions are wound in a direction opposite to said helical elements of another of said helical portions.
7. The stent of claim 1 wherein one or more pairs of helical portions are separated and flanked by said strut portions, said helical elements of one portion of said pair being wound in a direction opposite to said helical elements of the other portion of said pair.
8. The stent of claim 1 wherein said strut elements of said strut portion have a wave pattern of individual wave portions, each individual wave portion having a peak.
9. The stent of claim 8 wherein each of said helical elements is connected to a respective one of said peaks of said strut elements.
10. The stent of claim 8 wherein some of said helical elements are connected to some of said peaks of said strut elements.
11. The stent of claim 8 wherein every other one of said peaks of said strut elements are connected by a respective one of said helical elements.
12. The stent of claim 8 wherein said strut portion comprises a plurality of said strut elements and peaks of said individual wave members being connected to one another by a link.
13. The stent of claim 4 wherein at least one of said strut portions comprises a plurality of said strut elements, said strut elements of said strut portion have a wave pattern of individual wave portions, each individual wave portion having a peak and peaks of said individual wave members being connected to one another by a link.
14. The stent of claim 13 wherein said at least of said one strut portions is at either end of said stent.
15. The stent of claim 1 wherein said helical elements extend helically in a first direction from a first said strut element to a peak and then in an opposite direction from said peak to a second said strut element.
16. The stent of claim 1 further comprising one or more additional said helical portions and one or more additional said strut portions wherein one of said one or more additional said helical portions is connected to a second end of one of said strut portions, said one or more additional said helical portions being connected respectively to said one or more additional said strut portions such that each of said helical portions is interposed between a pair of said strut portions and at least one of said helical portions comprise helical elements which extend helically in a first direction from a first said strut portion to a peak and then in an opposite direction from said peak to a second said strut portion.
17. The stent of claim 16 wherein at least one of said helical portions comprises said helical elements being wound in a direction opposite to said helical elements of another of said helical portions.
18. The stent of claim 1 wherein said helical portion has a larger diameter than said strut portions.
19. The stent of claim 4 wherein at least one of said helical portions has a larger diameter than at least one of said strut portions.
20. The stent of claim 1 wherein said helical portion has a smaller diameter than said strut portion.
21. The stent of claim 4 wherein at least one of said helical portions has a smaller diameter than at least one of said strut portions.
22. The stent of claim 1 further comprising a biocompatible graft material covering an outside surface of said stent.
23. The stent of claim 1 further comprising a biocompatible graft material covering an inside surface of said stent.
24. The stent of claim 1 further comprising a biocompatible graft material covering and an outside surface and an inside surface of said stent.
25. The stent of claim 1 further comprising a biocompatible graft material attached to at least one of said strut portions, said graft material covering said strut portions and said helical portion.
26. The stent of claim 1 further comprising a plurality of sections of biocompatible graft material, each of said sections of graft material being attached to one of said strut portions and covering the attached said strut portion and a portion of an adjacent said helical portion wherein a gap is provided between each of said sections of graft material.
27. The stent of claim 26 wherein said gap is less than about 20% of a length of said helical portion.
28. The stent of claim 1 further comprising a plurality of sections of a biocompatible graft material, each of said sections of graft material being attached to one of said strut portions and covering the attached said strut portion and an adjacent said helical portion wherein said graft material of adjacent sections of graft material is overlapped.
29. The stent of claim 28 wherein said overlap is less than about 40% of a length of said helical portion.
30. The stent of claim 1 further comprising a biocompatible graft material, said graft material being attached to at least one of said strut portions, said graft material covering said strut portions and said helical portion and said graft material having a bulge at said helical portion.
31. The stent of claim 1 further comprising a biocompatible graft material, said graft material being attached to at least one of said strut portions, said graft material covering said strut portions and said helical portion and said graft material having a plurality longitudinal openings in said graft material over said helical portion.
32. The stent of claim 1 further comprising a biocompatible graft material, said graft material being attached to at least one of said strut portions and covering said strut portions and said helical portion, said graft material having a bulge at said helical portion and said graft material having a plurality of longitudinal openings in said graft material over said helical portion.
33. The stent of claim 32 further comprising a biocompatible graft material, said graft material being attached to at least one of said strut portions and covering said strut portions and said helical portion, said graft material having a plurality of helical openings corresponding to a pitch of said helical elements.
34. The stent of claim 1 further comprising a plurality of sections of biocompatible graft material each of said sections being attached to either said strut portion or said helical portion.
35. The stent of claim 34 wherein a gap is provided between each of said sections of said graft material.
36. The stent of claim 35 wherein said gap is less than about 20% of a length of said helical portion.
37. The stent of claim 1 further comprising a plurality of sections of biocompatible graft material each of said sections being attached to either said strut portion or said helical portion wherein adjacent sections of graft material are overlapped.
38. The stent of claim 37 wherein said overlap is less than about 40% of a length of said helical portion.
39. The stent of claim 1 wherein a gap between adjacent helical elements of a helical portion is about the same in a compressed state of said stent.
40. The stent of claim 39 wherein said gap is in a range of between 0 and a size of a gap between adjacent helical elements of a helical portion in said deployed state.
41. The stent of claim 1 wherein adjacent helical elements of a helical portion contact one another in a compressed state.
42. The stent of claim 1 wherein a gap between adjacent helical elements of a helical portion varies along the length of said helical portion in a compressed state.
43. The stent of claim 42 wherein said gap is in a range of between 0 and a size of a gap between adjacent helical elements of a helical portion in said deployed state.
44. The stent of claim 4 wherein said strut portions and/or said helical portions can have a varied axial length over a length of said stent.
45. The stent of claim 44 wherein said strut elements of said strut portion have a wave pattern of individual wave portions, each individual wave portion having a peak and each of said helical elements is connected to a respective one of said peaks on one side of said side strut elements and some of said helical elements are connected to some of said peaks on the other side of said side strut elements.
46. The stent of claim 45 wherein every other one of said peaks of said strut elements are connected by a respective one of said helical elements.
47. The stent of claim 4 wherein one of said helical portions has a higher ratio of a sum of gap lengths to a length of the helical portion than a second one of said helical portions.
48. The stent of claim 4 wherein one of said strut portions has less strut elements than a second of said strut portions.
49. The stent of claim 48 wherein said one of said strut portions has half as many strut elements as the second of said strut portions.
50. Flexible stent comprising:
a helical portion comprising a plurality of side-by-side, individual helical elements helically wound about an axis of said stent, said helical portion being expandable radially upon deployment and compressible, expandable and bendable in a deployed state; and a strut portion on either side of said helical portion, each of said strut portions comprising helically aligned strut elements having a first end connected to said helical elements of said helical portion, said strut portions being radially expandable upon deployment.
51. The stent of claim 50 wherein each of said helical elements extends for one or more complete rotations of 360 degrees about an axis of said stent.
52. The stent of claim 50 wherein each of said helical elements extends for at least 90 degrees about an axis of said stent.
53. A method for minimizing or eliminating foreshortening of a flexible stent comprising rotating a plurality of side-by-side individual helical elements, said helical elements being helically wound about an axis of said stent to form a helical portion, said helical portion being expandable radially upon deployment and compressible, expandable and bendable in a deployed state and a strut portion on either side of said helical portion, each of said strut portions comprising axially aligned strut elements having a first end connected to said helical elements of said helical portion, said strut portions being radially expandable upon deployment.
54. The method of claim 53 wherein an axial length of said stent in said deployed state is the same as an axial length of said stent in a crimped state.
55. The stent of claim 53 wherein a gap between said side-by-side helical elements of said helical portion is about the same in a crimped state of said stent.
56. The stent of claim 53 wherein said side-by-side helical elements of said helical portion contact one another in a crimped state of said stent.
57. The method of claim 56 wherein an axial length of said stent in said deployed state is the same as an axial length of said stent in a crimped state.
58. The method of claim 53 wherein an axial length of said stent in a crimped state is less than an axial length of said stent in said deployed state.
59. A method for crimping a flexible stent comprising elongating a plurality of side-by-side individual helical elements to a crimped state, said helical elements being helically wound about an axis of said stent to form a helical portion, said helical portion being expandable radially upon deployment and compressible, expandable and bendable in a deployed state and a strut portion on either side of said helical portion, each of said strut portions comprising axially aligned strut elements having a first end connected to said helical elements of said helical portion, said strut portions being radially expandable upon deployment.
60. The stent of claim 59 wherein a gap between said side-by-side helical elements of said helical portion varies along a length of said helical portion in said crimped state.
61. The method of claim 59 wherein an axial length of said stent in said deployed state is less than an axial length of said stent in said crimped state.
62. A method for placing a flexible stent within a mammal in a body lumen comprising placing one or more stents at said site, said flexible stent comprising a helical portion comprising a plurality of side-by-side, individual helical elements helically wound about an axis of said stent, said helical portion being expandable radially upon deployment and compressible, expandable and bendable in a deployed state; and a strut portion on either side of said helical portion, each of said strut portions comprising axially aligned strut elements having a first end connected to said helical elements of said helical section, said strut portions being radially expandable upon deployment.
63. The method of claim 62 wherein the mammal is a human and the body lumen is a vessel or duct.
64. The method of claim 62 wherein the mammal is a human and the body lumen is a super femoral artery.
65. The method of claim 62 wherein said stent further comprises a biocompatible graft material covering an outside surface of said stent and/or an inside surface of said stent.
66. A method of treating a diseased vessel or duct comprising the steps of:
guiding a catheter to a target site;
advancing through the catheter a flexible stent, said flexible stent comprising a helical portion comprising a plurality of side-by-side, individual helical elements helically wound about an axis of said stent, and a strut portion on either side of said helical portion, each of said strut portions comprising axially aligned strut elements having a first end connected to said helical elements of said helical section;
expelling the stent from the catheter at the target site, causing the helical portion to expand radially and said strut portions to expand radially, said helical portion being compressible, expandable and bendable in a deployed state.
67. The method of claim 66 wherein said target site is a vascular site.
68. The method of claim 66 wherein the target site is a super femoral artery.
69. The method of claim 66 wherein said target site is a lesion.
70. The method of claim 66 wherein said target site is an aneurysm.
71. The method of claim 66 wherein said stent further comprises a biocompatible graft material covering an outside surface of said stent and/or an inside surface of said stent.
72. The method of claim 66 wherein said stent further comprises a coating of a polymer and/or drug eluting material.
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Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20130268055A1 (en) * | 2012-03-07 | 2013-10-10 | Orbusneich Medical, Inc. | Medical device for implantation into luminal structures |
WO2014078536A1 (en) * | 2012-11-15 | 2014-05-22 | Palmaz Scientific, Inc. | Stents having a hybrid pattern and methods of manufacture |
WO2014066356A3 (en) * | 2012-10-22 | 2014-06-19 | Orbusneich Medical, Inc. | Medical device for implantation into luminal structures |
US8888841B2 (en) | 2010-06-21 | 2014-11-18 | Zorion Medical, Inc. | Bioabsorbable implants |
US20140379066A1 (en) * | 2005-04-04 | 2014-12-25 | Flexible Stenting Solutions, Inc. | Flexible stent |
US8986369B2 (en) | 2010-12-01 | 2015-03-24 | Zorion Medical, Inc. | Magnesium-based absorbable implants |
US9980835B2 (en) | 2013-10-22 | 2018-05-29 | Orbusneich Medical Inc. | Medical device for implantation into luminal structures incorporating corrugated structural elements |
Families Citing this family (91)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7887578B2 (en) | 1998-09-05 | 2011-02-15 | Abbott Laboratories Vascular Enterprises Limited | Stent having an expandable web structure |
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 |
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 |
US8382821B2 (en) | 1998-12-03 | 2013-02-26 | Medinol Ltd. | Helical hybrid stent |
US20040267349A1 (en) | 2003-06-27 | 2004-12-30 | Kobi Richter | Amorphous metal alloy medical devices |
WO2004026183A2 (en) | 2002-09-20 | 2004-04-01 | Nellix, Inc. | Stent-graft with positioning anchor |
US9039755B2 (en) * | 2003-06-27 | 2015-05-26 | Medinol Ltd. | Helical hybrid stent |
US9155639B2 (en) | 2009-04-22 | 2015-10-13 | Medinol Ltd. | Helical hybrid stent |
US7763065B2 (en) | 2004-07-21 | 2010-07-27 | Reva Medical, Inc. | Balloon expandable crush-recoverable stent device |
US8048145B2 (en) | 2004-07-22 | 2011-11-01 | Endologix, Inc. | Graft systems having filling structures supported by scaffolds and methods for their use |
US8597716B2 (en) * | 2009-06-23 | 2013-12-03 | Abbott Cardiovascular Systems Inc. | Methods to increase fracture resistance of a drug-eluting medical device |
US8292944B2 (en) | 2004-12-17 | 2012-10-23 | Reva Medical, Inc. | Slide-and-lock stent |
EP1903999B1 (en) | 2005-04-25 | 2018-11-21 | Covidien LP | Controlled fracture connections for stents |
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 |
US7914574B2 (en) | 2005-08-02 | 2011-03-29 | Reva Medical, Inc. | Axially nested slide and lock expandable device |
US9149378B2 (en) | 2005-08-02 | 2015-10-06 | Reva Medical, Inc. | Axially nested slide and lock expandable device |
US7704275B2 (en) | 2007-01-26 | 2010-04-27 | Reva Medical, Inc. | Circumferentially nested expandable device |
US20080221658A1 (en) * | 2007-03-09 | 2008-09-11 | Novostent Corporation | Vascular prosthesis and methods of use |
US8348994B2 (en) * | 2007-03-09 | 2013-01-08 | Novostent Corporation | Vascular prosthesis with alternating helical sections |
US8002815B2 (en) * | 2007-03-09 | 2011-08-23 | Novostent Corporation | Delivery system and method for vascular prosthesis |
US9017395B2 (en) * | 2007-03-09 | 2015-04-28 | Novostent Corporation | Vascular prosthesis and methods of use |
US8128679B2 (en) | 2007-05-23 | 2012-03-06 | Abbott Laboratories Vascular Enterprises Limited | Flexible stent with torque-absorbing connectors |
US8016874B2 (en) | 2007-05-23 | 2011-09-13 | Abbott Laboratories Vascular Enterprises Limited | Flexible stent with elevated scaffolding properties |
US7988723B2 (en) | 2007-08-02 | 2011-08-02 | Flexible Stenting Solutions, Inc. | Flexible stent |
JP5216098B2 (en) | 2007-11-30 | 2013-06-19 | レヴァ メディカル、 インコーポレイテッド | Axial and radially nested expandable device |
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 |
JP2011511701A (en) * | 2008-02-13 | 2011-04-14 | ネリックス・インコーポレーテッド | Graft inner frame with axially variable properties |
AU2009240419A1 (en) | 2008-04-25 | 2009-10-29 | Nellix, Inc. | Stent graft delivery system |
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 |
US10716573B2 (en) | 2008-05-01 | 2020-07-21 | Aneuclose | Janjua aneurysm net with a resilient neck-bridging portion for occluding a cerebral aneurysm |
US8974487B2 (en) | 2008-05-01 | 2015-03-10 | Aneuclose Llc | Aneurysm occlusion device |
US20090319029A1 (en) * | 2008-06-04 | 2009-12-24 | Nellix, Inc. | Docking apparatus and methods of use |
JP2011522615A (en) | 2008-06-04 | 2011-08-04 | ネリックス・インコーポレーテッド | Sealing device and method of use |
US20150039072A1 (en) * | 2008-07-31 | 2015-02-05 | Bradley Beach | Flexible stent |
CN102164565B (en) * | 2008-08-19 | 2014-07-23 | 帝秀简公司 | Self-expanding medical device |
WO2010024868A1 (en) * | 2008-08-27 | 2010-03-04 | Cook Incorporated | Multi-section stent |
US9149376B2 (en) | 2008-10-06 | 2015-10-06 | Cordis Corporation | Reconstrainable stent delivery system |
US9149377B2 (en) | 2008-10-10 | 2015-10-06 | Veryan Medical Ltd. | Stent suitable for deployment in a blood vessel |
EP2331014B1 (en) | 2008-10-10 | 2017-08-09 | Reva Medical, Inc. | Expandable slide and lock stent |
WO2010065241A1 (en) * | 2008-12-02 | 2010-06-10 | Boston Scientific Scimed, Inc. | Stent with graduated stiffness |
WO2010088676A1 (en) | 2009-02-02 | 2010-08-05 | Cordis Corporation | Flexible stent design |
WO2010124286A1 (en) * | 2009-04-24 | 2010-10-28 | Flexible Stenting Solutions, Inc. | Flexible devices |
EP2429453B1 (en) * | 2009-05-14 | 2021-01-27 | Orbusneich Medical Pte. Ltd | Self-expanding stent with polygon transition zone |
US8366765B2 (en) * | 2009-09-18 | 2013-02-05 | Medtronic Vascular, Inc. | Helical stent with connections |
US8114149B2 (en) * | 2009-10-20 | 2012-02-14 | Svelte Medical Systems, Inc. | Hybrid stent with helical connectors |
US9649211B2 (en) | 2009-11-04 | 2017-05-16 | Confluent Medical Technologies, Inc. | Alternating circumferential bridge stent design and methods for use thereof |
US10092427B2 (en) | 2009-11-04 | 2018-10-09 | Confluent Medical Technologies, Inc. | Alternating circumferential bridge stent design and methods for use thereof |
US9358140B1 (en) | 2009-11-18 | 2016-06-07 | Aneuclose Llc | Stent with outer member to embolize an aneurysm |
US8348987B2 (en) * | 2009-12-22 | 2013-01-08 | Cook Medical Technologies Llc | Balloon with scoring member |
US20110276078A1 (en) | 2009-12-30 | 2011-11-10 | Nellix, Inc. | Filling structure for a graft system and methods of use |
US8906057B2 (en) | 2010-01-04 | 2014-12-09 | Aneuclose Llc | Aneurysm embolization by rotational accumulation of mass |
WO2011127452A1 (en) | 2010-04-10 | 2011-10-13 | Reva Medical, Inc | Expandable slide and lock stent |
US8864811B2 (en) | 2010-06-08 | 2014-10-21 | Veniti, Inc. | Bi-directional stent delivery system |
US9301864B2 (en) | 2010-06-08 | 2016-04-05 | Veniti, Inc. | Bi-directional stent delivery system |
US20120022578A1 (en) * | 2010-07-20 | 2012-01-26 | Cook Medical Technologies Llc | Frame-based vena cava filter |
JP5902165B2 (en) * | 2010-08-02 | 2016-04-13 | コーディス・コーポレイションCordis Corporation | Flexible spiral stent with different spiral regions |
US9233014B2 (en) * | 2010-09-24 | 2016-01-12 | Veniti, Inc. | Stent with support braces |
US8801768B2 (en) | 2011-01-21 | 2014-08-12 | Endologix, Inc. | Graft systems having semi-permeable filling structures and methods for their use |
US9028540B2 (en) | 2011-03-25 | 2015-05-12 | Covidien Lp | Vascular stent with improved vessel wall apposition |
EP2693980B1 (en) | 2011-04-06 | 2022-07-13 | Endologix LLC | System for endovascular aneurysm treatment |
US9138232B2 (en) | 2011-05-24 | 2015-09-22 | Aneuclose Llc | Aneurysm occlusion by rotational dispensation of mass |
CN102335052A (en) * | 2011-07-15 | 2012-02-01 | 南京微创医学科技有限公司 | Anti-restenosis digestive tract stent |
NZ716708A (en) | 2012-05-14 | 2016-08-26 | Bard Inc C R | Uniformly expandable stent |
US9254205B2 (en) | 2012-09-27 | 2016-02-09 | Covidien Lp | Vascular stent with improved vessel wall apposition |
USD723165S1 (en) | 2013-03-12 | 2015-02-24 | C. R. Bard, Inc. | Stent |
CA2905515C (en) | 2013-03-14 | 2020-11-10 | Palmaz Scientific, Inc. | Monolithic medical devices, methods of making and using the same |
US9408732B2 (en) | 2013-03-14 | 2016-08-09 | Reva Medical, Inc. | Reduced-profile slide and lock stent |
JP6533776B2 (en) | 2013-03-14 | 2019-06-19 | エンドーロジックス インコーポレイテッド | System for treating an aneurysm in a patient's body and method of operating the same |
DE102013104062A1 (en) | 2013-04-22 | 2014-10-23 | Novatech Sa | stent |
CN105451691B (en) * | 2013-06-21 | 2018-07-17 | 波士顿科学国际有限公司 | Holder with deflection connector |
JP5586742B1 (en) * | 2013-06-28 | 2014-09-10 | 株式会社World Medish | High flexibility stent |
EP3184084B1 (en) | 2013-09-12 | 2020-04-01 | Boston Scientific Scimed, Inc. | Stent with anti-migration connectors |
JP5550028B1 (en) * | 2014-01-27 | 2014-07-16 | 株式会社World Medish | High flexibility stent |
JP5695259B1 (en) | 2014-02-19 | 2015-04-01 | 株式会社World Medish | High flexibility stent |
USD888245S1 (en) | 2014-03-14 | 2020-06-23 | Vactronix Scientific, Llc | Stent device |
CN106456347B (en) | 2014-03-18 | 2018-11-13 | 波士顿科学国际有限公司 | Reduce the support Design of granulation and inflammation |
US10219921B2 (en) | 2014-10-02 | 2019-03-05 | Boston Scientific Scimed, Inc. | Controlled ingrowth feature for antimigration |
JP2017530811A (en) | 2014-10-22 | 2017-10-19 | ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. | Flexible hinged stent |
WO2016073597A1 (en) | 2014-11-06 | 2016-05-12 | Boston Scientific Scimed, Inc. | Tracheal stent |
CN104490500B (en) * | 2014-12-25 | 2017-01-18 | 周玉杰 | Chain type coronary stent suitable for coronary artery tortuosity angulation lesion |
JP6734097B2 (en) * | 2015-03-31 | 2020-08-05 | 康宏 正林 | Highly flexible stent |
EP3763340A1 (en) * | 2016-03-24 | 2021-01-13 | Covidien LP | Vascular flow diversion |
US11628077B2 (en) * | 2016-10-31 | 2023-04-18 | Razmodics Llc | Post deployment radial force recovery of biodegradable scaffolds |
US10342686B2 (en) * | 2017-08-10 | 2019-07-09 | Covidien Lp | Thin film mesh hybrid for treating vascular defects |
CN109662819B (en) * | 2019-01-31 | 2021-08-06 | 深圳市科奕顿生物医疗科技有限公司 | Self-expanding stent and preparation method and application thereof |
CN109662820B (en) * | 2019-01-31 | 2023-06-16 | 深圳市科奕顿生物医疗科技有限公司 | Self-expanding stent and preparation method and application thereof |
JP2023510553A (en) | 2020-01-13 | 2023-03-14 | 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 | anti-migration stent |
CN113017753A (en) * | 2021-02-26 | 2021-06-25 | 珠海通桥医疗科技有限公司 | Blood vessel support |
Citations (55)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5102417A (en) * | 1985-11-07 | 1992-04-07 | Expandable Grafts Partnership | Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft |
US5383892A (en) * | 1991-11-08 | 1995-01-24 | Meadox France | Stent for transluminal implantation |
US5449373A (en) * | 1994-03-17 | 1995-09-12 | Medinol Ltd. | Articulated stent |
US5545210A (en) * | 1994-09-22 | 1996-08-13 | Advanced Coronary Technology, Inc. | Method of implanting a permanent shape memory alloy stent |
US5669932A (en) * | 1996-05-29 | 1997-09-23 | Isostent, Inc. | Means for accurately positioning an expandable stent |
US5693085A (en) * | 1994-04-29 | 1997-12-02 | Scimed Life Systems, Inc. | Stent with collagen |
US5749919A (en) * | 1994-01-10 | 1998-05-12 | Microfil Industries S.A. | Resilient prosthesis for widening a channel, particularly a blood vessel, and method for making same |
US5755781A (en) * | 1996-08-06 | 1998-05-26 | Iowa-India Investments Company Limited | Embodiments of multiple interconnected stents |
US5810872A (en) * | 1997-03-14 | 1998-09-22 | Kanesaka; Nozomu | Flexible stent |
US5824059A (en) * | 1997-08-05 | 1998-10-20 | Wijay; Bandula | Flexible stent |
US5911754A (en) * | 1998-07-24 | 1999-06-15 | Uni-Cath Inc. | Flexible stent with effective strut and connector patterns |
US6033433A (en) * | 1997-04-25 | 2000-03-07 | Scimed Life Systems, Inc. | Stent configurations including spirals |
US6039756A (en) * | 1996-04-26 | 2000-03-21 | Jang; G. David | Intravascular stent |
US6042597A (en) * | 1998-10-23 | 2000-03-28 | Scimed Life Systems, Inc. | Helical stent design |
US6146417A (en) * | 1996-08-22 | 2000-11-14 | Ischinger; Thomas | Tubular stent |
US6152957A (en) * | 1996-04-26 | 2000-11-28 | Jang; G. David | Intravascular stent |
US6231598B1 (en) * | 1997-09-24 | 2001-05-15 | Med Institute, Inc. | Radially expandable stent |
US6241762B1 (en) * | 1998-03-30 | 2001-06-05 | Conor Medsystems, Inc. | Expandable medical device with ductile hinges |
US6245101B1 (en) * | 1999-05-03 | 2001-06-12 | William J. Drasler | Intravascular hinge stent |
US6261319B1 (en) * | 1998-07-08 | 2001-07-17 | Scimed Life Systems, Inc. | Stent |
US6302907B1 (en) * | 1999-10-05 | 2001-10-16 | Scimed Life Systems, Inc. | Flexible endoluminal stent and process of manufacture |
US20010039447A1 (en) * | 2000-03-01 | 2001-11-08 | Pinchasik Gregory A. | Longitudinally flexible stent |
US6352552B1 (en) * | 2000-05-02 | 2002-03-05 | Scion Cardio-Vascular, Inc. | Stent |
US20020082682A1 (en) * | 2000-12-19 | 2002-06-27 | Vascular Architects, Inc. | Biologically active agent delivery apparatus and method |
US20020095207A1 (en) * | 2001-01-15 | 2002-07-18 | Yousuke Moriuchi | Stent |
US6423091B1 (en) * | 2000-05-16 | 2002-07-23 | Cordis Corporation | Helical stent having flat ends |
US20020143390A1 (en) * | 2001-03-30 | 2002-10-03 | Tatsuzo Ishii | Stent |
US6551351B2 (en) * | 1999-07-02 | 2003-04-22 | Scimed Life Systems | Spiral wound stent |
US20030114920A1 (en) * | 1999-12-21 | 2003-06-19 | Caro Colin Gerald | Vascular stents |
US6585758B1 (en) * | 1999-11-16 | 2003-07-01 | Scimed Life Systems, Inc. | Multi-section filamentary endoluminal stent |
US20030144729A1 (en) * | 2002-01-30 | 2003-07-31 | Scimed Life Systems, Inc. | Stent with wishbone connectors and serpentine bands |
US6602281B1 (en) * | 1995-06-05 | 2003-08-05 | Avantec Vascular Corporation | Radially expansible vessel scaffold having beams and expansion joints |
US6632236B2 (en) * | 1999-03-12 | 2003-10-14 | Arteria Medical Science, Inc. | Catheter having radially expandable main body |
US20030195609A1 (en) * | 2002-04-10 | 2003-10-16 | Scimed Life Systems, Inc. | Hybrid stent |
US20030204244A1 (en) * | 2002-04-26 | 2003-10-30 | Stiger Mark L. | Aneurysm exclusion stent |
US20040002753A1 (en) * | 2002-06-28 | 2004-01-01 | Robert Burgermeister | Stent with diagonal flexible connecting links |
US6679911B2 (en) * | 2001-03-01 | 2004-01-20 | Cordis Corporation | Flexible stent |
US20040034402A1 (en) * | 2002-07-26 | 2004-02-19 | Syntheon, Llc | Helical stent having flexible transition zone |
US20040088044A1 (en) * | 1995-03-01 | 2004-05-06 | Scimed Life Systems, Inc. | Longitudinally flexible expandable stent |
US20040122504A1 (en) * | 2002-12-24 | 2004-06-24 | Michael Hogendijk | Vascular prosthesis and methods of use |
US20040172123A1 (en) * | 2002-12-20 | 2004-09-02 | Biotronik Gmbh & Co. Kg | Stent |
US20040186556A1 (en) * | 2002-12-24 | 2004-09-23 | Novostent Corporation | Vascular prosthesis and methods of use |
US20050033410A1 (en) * | 2002-12-24 | 2005-02-10 | Novostent Corporation | Vascular prothesis having flexible configuration |
US6878162B2 (en) * | 2002-08-30 | 2005-04-12 | Edwards Lifesciences Ag | Helical stent having improved flexibility and expandability |
US20060020322A1 (en) * | 2004-07-21 | 2006-01-26 | Alexander Leynov | Expandable framework with overlapping connectors |
US20060247759A1 (en) * | 2005-04-04 | 2006-11-02 | Janet Burpee | Flexible stent |
US7131993B2 (en) * | 2003-06-25 | 2006-11-07 | Boston Scientific Scimed, Inc. | Varying circumferential spanned connectors in a stent |
US7169175B2 (en) * | 2000-05-22 | 2007-01-30 | Orbusneich Medical, Inc. | Self-expanding stent |
US7179286B2 (en) * | 2003-02-21 | 2007-02-20 | Boston Scientific Scimed, Inc. | Stent with stepped connectors |
US7208009B2 (en) * | 1996-12-26 | 2007-04-24 | Medinol, Ltd. | Stent fabrication method |
US7217286B2 (en) * | 1997-04-18 | 2007-05-15 | Cordis Corporation | Local delivery of rapamycin for treatment of proliferative sequelae associated with PTCA procedures, including delivery using a modified stent |
US20070129786A1 (en) * | 2005-10-14 | 2007-06-07 | Bradley Beach | Helical stent |
US20090036976A1 (en) * | 2007-08-02 | 2009-02-05 | Bradley Beach | Flexible stent |
US7637939B2 (en) * | 2005-06-30 | 2009-12-29 | Boston Scientific Scimed, Inc. | Hybrid stent |
US20100286760A1 (en) * | 2009-04-24 | 2010-11-11 | Bradley Beach | Flexible devices |
Family Cites Families (210)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4425908A (en) | 1981-10-22 | 1984-01-17 | Beth Israel Hospital | Blood clot filter |
US4432132A (en) * | 1981-12-07 | 1984-02-21 | Bell Telephone Laboratories, Incorporated | Formation of sidewall oxide layers by reactive oxygen ion etching to define submicron features |
US4665906A (en) | 1983-10-14 | 1987-05-19 | Raychem Corporation | Medical devices incorporating sim alloy elements |
US5190546A (en) | 1983-10-14 | 1993-03-02 | Raychem Corporation | Medical devices incorporating SIM alloy elements |
US5275622A (en) | 1983-12-09 | 1994-01-04 | Harrison Medical Technologies, Inc. | Endovascular grafting apparatus, system and method and devices for use therewith |
US4813925A (en) | 1987-04-21 | 1989-03-21 | Medical Engineering Corporation | Spiral ureteral stent |
US5133732A (en) | 1987-10-19 | 1992-07-28 | Medtronic, Inc. | Intravascular stent |
US5266073A (en) | 1987-12-08 | 1993-11-30 | Wall W Henry | Angioplasty stent |
CA2026604A1 (en) | 1989-10-02 | 1991-04-03 | Rodney G. Wolff | Articulated stent |
US5190540A (en) | 1990-06-08 | 1993-03-02 | Cardiovascular & Interventional Research Consultants, Inc. | Thermal balloon angioplasty |
US5197978B1 (en) | 1991-04-26 | 1996-05-28 | Advanced Coronary Tech | Removable heat-recoverable tissue supporting device |
US5507767A (en) | 1992-01-15 | 1996-04-16 | Cook Incorporated | Spiral stent |
US5683448A (en) | 1992-02-21 | 1997-11-04 | Boston Scientific Technology, Inc. | Intraluminal stent and graft |
WO1995014500A1 (en) | 1992-05-01 | 1995-06-01 | Beth Israel Hospital | A stent |
CA2157936C (en) | 1993-03-11 | 2004-11-02 | Gregory Pinchasik | Stent |
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 |
US5989280A (en) | 1993-10-22 | 1999-11-23 | Scimed Lifesystems, Inc | Stent delivery apparatus and method |
US5733303A (en) | 1994-03-17 | 1998-03-31 | Medinol Ltd. | Flexible expandable stent |
US5843120A (en) | 1994-03-17 | 1998-12-01 | Medinol Ltd. | Flexible-expandable stent |
EP0997115B1 (en) * | 1994-04-01 | 2003-10-29 | Prograft Medical, Inc. | Self-expandable stent and stent-graft and method of preparing them |
US6165210A (en) | 1994-04-01 | 2000-12-26 | Gore Enterprise Holdings, Inc. | Self-expandable helical intravascular stent and stent-graft |
US5824041A (en) | 1994-06-08 | 1998-10-20 | Medtronic, Inc. | Apparatus and methods for placement and repositioning of intraluminal prostheses |
DE69528216T2 (en) | 1994-06-17 | 2003-04-17 | Terumo Corp | Process for the production of a permanent stent |
EP0794726A4 (en) | 1994-10-20 | 1998-01-07 | Instent Inc | Cystoscope delivery system |
US5836964A (en) | 1996-10-30 | 1998-11-17 | Medinol Ltd. | Stent fabrication method |
IL115756A0 (en) * | 1994-10-27 | 1996-01-19 | Medinol Ltd | Stent fabrication method |
CA2301351C (en) | 1994-11-28 | 2002-01-22 | Advanced Cardiovascular Systems, Inc. | Method and apparatus for direct laser cutting of metal stents |
US5591226A (en) | 1995-01-23 | 1997-01-07 | Schneider (Usa) Inc. | Percutaneous stent-graft and method for delivery thereof |
ATE220308T1 (en) | 1995-03-01 | 2002-07-15 | Scimed Life Systems Inc | LONGITUDONLY FLEXIBLE AND EXPANDABLE STENT |
US6896696B2 (en) | 1998-11-20 | 2005-05-24 | Scimed Life Systems, Inc. | Flexible and expandable stent |
US5591197A (en) | 1995-03-14 | 1997-01-07 | Advanced Cardiovascular Systems, Inc. | Expandable stent forming projecting barbs and method for deploying |
WO1996032078A1 (en) | 1995-04-14 | 1996-10-17 | Schneider (Usa) Inc. | Rolling membrane stent delivery device |
CZ292021B6 (en) * | 1995-04-26 | 2003-07-16 | Medinol Ltd. | Connector for connecting adjacent areas of adjacent segments of an articulated stent and the articulated stent per se |
CN1140227C (en) * | 1995-04-26 | 2004-03-03 | 梅迪诺尔有限公司 | Articulated stent |
US5788707A (en) | 1995-06-07 | 1998-08-04 | Scimed Life Systems, Inc. | Pull back sleeve system with compression resistant inner shaft |
US5776161A (en) | 1995-10-16 | 1998-07-07 | Instent, Inc. | Medical stents, apparatus and method for making same |
WO1997014375A1 (en) | 1995-10-20 | 1997-04-24 | Bandula Wijay | Vascular stent |
US5913896A (en) | 1995-11-28 | 1999-06-22 | Medtronic, Inc. | Interwoven dual sinusoidal helix stent |
ZA9610721B (en) | 1995-12-21 | 1998-06-19 | Cornell Res Foundation Inc | Grapevine leafroll virus proteins and their uses. |
EP1011889B1 (en) | 1996-01-30 | 2002-10-30 | Medtronic, Inc. | Articles for and methods of making stents |
WO1997032544A1 (en) | 1996-03-05 | 1997-09-12 | Divysio Solutions Ulc. | Expandable stent and method for delivery of same |
JP3815622B2 (en) | 1996-03-07 | 2006-08-30 | エム イー ディー インスティチュート,インク | Inflatable stent |
US6334871B1 (en) | 1996-03-13 | 2002-01-01 | Medtronic, Inc. | Radiopaque stent markers |
IL117472A0 (en) | 1996-03-13 | 1996-07-23 | Instent Israel Ltd | Radiopaque stent markers |
US5649949A (en) | 1996-03-14 | 1997-07-22 | Target Therapeutics, Inc. | Variable cross-section conical vasoocclusive coils |
US5833699A (en) | 1996-04-10 | 1998-11-10 | Chuter; Timothy A. M. | Extending ribbon stent |
FR2747301B1 (en) | 1996-04-10 | 1998-09-18 | Nycomed Lab Sa | IMPLANTABLE DEVICE FOR MAINTAINING OR RE-ESTABLISHING THE NORMAL PASSAGE SECTION OF A BODY DUCT, AS WELL AS A SYSTEM FOR ITS PLACEMENT |
US5697971A (en) | 1996-06-11 | 1997-12-16 | Fischell; Robert E. | Multi-cell stent with cells having differing characteristics |
US5807404A (en) | 1996-09-19 | 1998-09-15 | Medinol Ltd. | Stent with variable features to optimize support and method of making such stent |
US6325826B1 (en) | 1998-01-14 | 2001-12-04 | Advanced Stent Technologies, Inc. | Extendible stent apparatus |
US5776142A (en) | 1996-12-19 | 1998-07-07 | Medtronic, Inc. | Controllable stent delivery system and method |
US6551350B1 (en) | 1996-12-23 | 2003-04-22 | Gore Enterprise Holdings, Inc. | Kink resistant bifurcated prosthesis |
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 |
US6241757B1 (en) | 1997-02-04 | 2001-06-05 | Solco Surgical Instrument Co., Ltd. | Stent for expanding body's lumen |
US5827321A (en) | 1997-02-07 | 1998-10-27 | Cornerstone Devices, Inc. | Non-Foreshortening intraluminal prosthesis |
DE69839498D1 (en) | 1997-02-11 | 2008-06-26 | Warsaw Orthopedic Inc | Plate for the anterior cervical spine with fixation system for one screw |
FR2760351B1 (en) | 1997-03-04 | 1999-05-28 | Bernard Glatt | HELICAL STENT FORMING DEVICE AND MANUFACTURING METHOD THEREOF |
US5911732A (en) | 1997-03-10 | 1999-06-15 | Johnson & Johnson Interventional Systems, Co. | Articulated expandable intraluminal stent |
US5792144A (en) | 1997-03-31 | 1998-08-11 | Cathco, Inc. | Stent delivery catheter system |
US5718713A (en) | 1997-04-10 | 1998-02-17 | Global Therapeutics, Inc. | Surgical stent having a streamlined contour |
US5741327A (en) | 1997-05-06 | 1998-04-21 | Global Therapeutics, Inc. | Surgical stent featuring radiopaque markers |
DE29708879U1 (en) | 1997-05-20 | 1997-07-31 | Jomed Implantate Gmbh | Coronary stent |
US5891192A (en) | 1997-05-22 | 1999-04-06 | The Regents Of The University Of California | Ion-implanted protein-coated intralumenal implants |
BE1011180A6 (en) | 1997-05-27 | 1999-06-01 | Medicorp R & D Benelux Sa | Luminal endoprosthesis AUTO EXPANDABLE. |
US5913895A (en) | 1997-06-02 | 1999-06-22 | Isostent, Inc. | Intravascular stent with enhanced rigidity strut members |
EP0884029B1 (en) | 1997-06-13 | 2004-12-22 | Gary J. Becker | Expandable intraluminal endoprosthesis |
US5843175A (en) | 1997-06-13 | 1998-12-01 | Global Therapeutics, Inc. | Enhanced flexibility surgical stent |
EP0890346A1 (en) | 1997-06-13 | 1999-01-13 | Gary J. Becker | Expandable intraluminal endoprosthesis |
FR2764794B1 (en) | 1997-06-20 | 1999-11-12 | Nycomed Lab Sa | EXPANDED TUBULAR DEVICE WITH VARIABLE THICKNESS |
IL121316A (en) | 1997-07-15 | 2001-07-24 | Litana Ltd | Implantable medical device of shape memory alloy |
US6340367B1 (en) | 1997-08-01 | 2002-01-22 | Boston Scientific Scimed, Inc. | Radiopaque markers and methods of using the same |
NO311781B1 (en) | 1997-11-13 | 2002-01-28 | Medinol Ltd | Metal multilayer stents |
US6156062A (en) | 1997-12-03 | 2000-12-05 | Ave Connaught | Helically wrapped interlocking stent |
US6022374A (en) | 1997-12-16 | 2000-02-08 | Cardiovasc, Inc. | Expandable stent having radiopaque marker and method |
US6626939B1 (en) | 1997-12-18 | 2003-09-30 | Boston Scientific Scimed, Inc. | Stent-graft with bioabsorbable structural support |
US6190406B1 (en) | 1998-01-09 | 2001-02-20 | Nitinal Development Corporation | Intravascular stent having tapered struts |
US6719779B2 (en) | 2000-11-07 | 2004-04-13 | Innercool Therapies, Inc. | Circulation set for temperature-controlled catheter and method of using the same |
US6533807B2 (en) | 1998-02-05 | 2003-03-18 | Medtronic, Inc. | Radially-expandable stent and delivery system |
US6676696B1 (en) | 1998-02-12 | 2004-01-13 | Thomas R. Marotta | Endovascular prosthesis |
JP4801838B2 (en) | 1998-03-05 | 2011-10-26 | ボストン サイエンティフィック リミテッド | Intraluminal stent |
US6019778A (en) | 1998-03-13 | 2000-02-01 | Cordis Corporation | Delivery apparatus for a self-expanding stent |
US7179289B2 (en) | 1998-03-30 | 2007-02-20 | Conor Medsystems, Inc. | Expandable medical device for delivery of beneficial agent |
US6264687B1 (en) | 1998-04-20 | 2001-07-24 | Cordis Corporation | Multi-laminate stent having superelastic articulated sections |
US6168621B1 (en) | 1998-05-29 | 2001-01-02 | Scimed Life Systems, Inc. | Balloon expandable stent with a self-expanding portion |
US6740113B2 (en) | 1998-05-29 | 2004-05-25 | Scimed Life Systems, Inc. | Balloon expandable stent with a self-expanding portion |
CA2334223C (en) | 1998-06-04 | 2008-11-18 | New York University | Endovascular thin film devices and methods for treating and preventing stroke |
DE19839646A1 (en) | 1998-08-31 | 2000-03-09 | Jomed Implantate Gmbh | Stent |
US6093194A (en) | 1998-09-14 | 2000-07-25 | Endocare, Inc. | Insertion device for stents and methods for use |
DE29816878U1 (en) | 1998-09-21 | 1998-12-24 | Schmitz Rode Thomas Dipl Ing D | Helix stent that can be manufactured using the cutting process |
US6059813A (en) | 1998-11-06 | 2000-05-09 | Scimed Life Systems, Inc. | Rolling membrane stent delivery system |
US6544278B1 (en) | 1998-11-06 | 2003-04-08 | Scimed Life Systems, Inc. | Rolling membrane stent delivery system |
CA2289169A1 (en) | 1998-11-11 | 2000-05-11 | Ogawa Spring Co., Ltd. | Stent, manufacturing method thereof and indwelling method thereof |
WO2000030563A1 (en) * | 1998-11-20 | 2000-06-02 | Scimed Life Systems, Inc. | Longitudinally flexible expandable stent |
SG75982A1 (en) | 1998-12-03 | 2000-10-24 | Medinol Ltd | Controlled detachment stents |
US6503270B1 (en) | 1998-12-03 | 2003-01-07 | Medinol Ltd. | Serpentine coiled ladder stent |
US6355059B1 (en) | 1998-12-03 | 2002-03-12 | Medinol, Ltd. | Serpentine coiled ladder stent |
US6743252B1 (en) | 1998-12-18 | 2004-06-01 | Cook Incorporated | Cannula stent |
US6254609B1 (en) | 1999-01-11 | 2001-07-03 | Scimed Life Systems, Inc. | Self-expanding stent delivery system with two sheaths |
EP1020166A1 (en) | 1999-01-12 | 2000-07-19 | Orbus Medical Technologies, Inc. | Expandable intraluminal endoprosthesis |
US6287333B1 (en) | 1999-03-15 | 2001-09-11 | Angiodynamics, Inc. | Flexible stent |
US6899730B1 (en) | 1999-04-15 | 2005-05-31 | Scimed Life Systems, Inc. | Catheter-stent device |
US6860899B1 (en) | 1999-04-15 | 2005-03-01 | Boston Scientific Scimed, Inc. | Method for treating neurovascular aneurysms |
US6730116B1 (en) | 1999-04-16 | 2004-05-04 | Medtronic, Inc. | Medical device for intraluminal endovascular stenting |
US6273911B1 (en) | 1999-04-22 | 2001-08-14 | Advanced Cardiovascular Systems, Inc. | Variable strength stent |
US6673103B1 (en) | 1999-05-20 | 2004-01-06 | Scimed Life Systems, Inc. | Mesh and stent for increased flexibility |
US6485507B1 (en) | 1999-07-28 | 2002-11-26 | Scimed Life Systems | Multi-property nitinol by heat treatment |
US6142987A (en) | 1999-08-03 | 2000-11-07 | Scimed Life Systems, Inc. | Guided filter with support wire and methods of use |
WO2001026584A1 (en) | 1999-10-14 | 2001-04-19 | United Stenting, Inc. | Stents with multilayered struts |
US6171328B1 (en) | 1999-11-09 | 2001-01-09 | Embol-X, Inc. | Intravascular catheter filter with interlocking petal design and methods of use |
US6264671B1 (en) | 1999-11-15 | 2001-07-24 | Advanced Cardiovascular Systems, Inc. | Stent delivery catheter and method of use |
CN1186423C (en) | 1999-12-03 | 2005-01-26 | 中国科学院南京土壤研究所 | Process for preparing ammonia suppressing film of rice field |
US6334866B1 (en) | 2000-01-14 | 2002-01-01 | William H. Wall | Stent device for performing endovascular repair of aneurysms |
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 |
US6723119B2 (en) | 2000-03-01 | 2004-04-20 | Medinol Ltd. | Longitudinally flexible stent |
US6953476B1 (en) | 2000-03-27 | 2005-10-11 | Neovasc Medical Ltd. | Device and method for treating ischemic heart disease |
US8236048B2 (en) | 2000-05-12 | 2012-08-07 | Cordis Corporation | Drug/drug delivery systems for the prevention and treatment of vascular disease |
AU2001275100A1 (en) | 2000-05-31 | 2001-12-11 | Courtney, Brian K. | Embolization protection system for vascular procedures |
US8298257B2 (en) | 2000-06-29 | 2012-10-30 | Concentric Medical, Inc. | Systems, methods and devices for removing obstructions from a blood vessel |
US6540775B1 (en) | 2000-06-30 | 2003-04-01 | Cordis Corporation | Ultraflexible open cell stent |
US6969401B1 (en) | 2000-08-18 | 2005-11-29 | Marotta Thomas R | Endovascular prosthesis |
US6565595B1 (en) | 2000-09-18 | 2003-05-20 | Scimed Life Systems, Inc. | Two component sleeves |
US6607552B1 (en) | 2000-09-18 | 2003-08-19 | Scimed Life Systems, Inc. | Rolling socks |
US6805898B1 (en) | 2000-09-28 | 2004-10-19 | Advanced Cardiovascular Systems, Inc. | Surface features of an implantable medical device |
US6492615B1 (en) | 2000-10-12 | 2002-12-10 | Scimed Life Systems, Inc. | Laser polishing of medical devices |
US7163552B2 (en) | 2000-10-13 | 2007-01-16 | Medtronic Vascular, Inc. | Stent delivery system with hydraulic deployment |
US6663664B1 (en) | 2000-10-26 | 2003-12-16 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent with time variable radial force |
US6506211B1 (en) | 2000-11-13 | 2003-01-14 | Scimed Life Systems, Inc. | Stent designs |
US6843802B1 (en) | 2000-11-16 | 2005-01-18 | Cordis Corporation | Delivery apparatus for a self expanding retractable stent |
US6579308B1 (en) | 2000-11-28 | 2003-06-17 | Scimed Life Systems, Inc. | Stent devices with detachable distal or proximal wires |
US6517567B2 (en) | 2000-11-30 | 2003-02-11 | Albert R. Bass, Jr. | Apparatus and method for pacifier withdrawal |
JP4727070B2 (en) | 2001-06-01 | 2011-07-20 | テルモ株式会社 | Stent |
JP4323102B2 (en) | 2001-01-15 | 2009-09-02 | テルモ株式会社 | Flexible stent |
US7169165B2 (en) | 2001-01-16 | 2007-01-30 | Boston Scientific Scimed, Inc. | Rapid exchange sheath for deployment of medical devices and methods of use |
US6899727B2 (en) | 2001-01-22 | 2005-05-31 | Gore Enterprise Holdings, Inc. | Deployment system for intraluminal devices |
US6736839B2 (en) | 2001-02-01 | 2004-05-18 | Charles Cummings | Medical device delivery system |
US6563080B2 (en) | 2001-02-15 | 2003-05-13 | Scimed Life Systems, Inc. | Laser cutting of stents and other medical devices |
US6613077B2 (en) | 2001-03-27 | 2003-09-02 | Scimed Life Systems, Inc. | Stent with controlled expansion |
GB0107910D0 (en) | 2001-03-29 | 2001-05-23 | Isis Innovation | Deployable stent |
US7105199B2 (en) | 2001-05-11 | 2006-09-12 | Exogenesis Corporation | Methods of adhering drugs to the surface of medical devices through ion beam surface modification |
US6599314B2 (en) | 2001-06-08 | 2003-07-29 | Cordis Corporation | Apparatus and method for stenting a vessel using balloon-actuated stent with interlocking elements |
US6612012B2 (en) | 2001-06-11 | 2003-09-02 | Cordis Neurovascular, Inc. | Method of manufacturing small profile medical devices |
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 |
US6796999B2 (en) | 2001-09-06 | 2004-09-28 | Medinol Ltd. | Self articulating stent |
IL160817A0 (en) | 2001-09-10 | 2004-08-31 | Medinol Ltd | Longitudinally flexible stent |
US7175655B1 (en) | 2001-09-17 | 2007-02-13 | Endovascular Technologies, Inc. | Avoiding stress-induced martensitic transformation in nickel titanium alloys used in medical devices |
US20030229390A1 (en) | 2001-09-17 | 2003-12-11 | Control Delivery Systems, Inc. | On-stent delivery of pyrimidines and purine analogs |
JP3605388B2 (en) | 2001-10-16 | 2004-12-22 | 川澄化学工業株式会社 | Stent |
US20050070992A1 (en) | 2001-11-28 | 2005-03-31 | Aptus Endosystems, Inc. | Prosthesis systems and methods sized and configured for the receipt and retention of fasteners |
JP4331610B2 (en) | 2001-12-20 | 2009-09-16 | トリバスキュラー2,インコーポレイティド | Advanced endovascular graft |
US7163553B2 (en) | 2001-12-28 | 2007-01-16 | Advanced Cardiovascular Systems, Inc. | Intravascular stent and method of use |
US6981985B2 (en) | 2002-01-22 | 2006-01-03 | Boston Scientific Scimed, Inc. | Stent bumper struts |
US7445629B2 (en) | 2002-01-31 | 2008-11-04 | Boston Scientific Scimed, Inc. | Medical device for delivering biologically active material |
US7169170B2 (en) | 2002-02-22 | 2007-01-30 | Cordis Corporation | Self-expanding stent delivery system |
US7052511B2 (en) | 2002-04-04 | 2006-05-30 | Scimed Life Systems, Inc. | Delivery system and method for deployment of foreshortening endoluminal devices |
DE10219014A1 (en) | 2002-04-27 | 2003-11-13 | Ruesch Willy Gmbh | Self-expanding stent for reinforcing and/or keeping open a hollow organ comprise two elastic tubular layers which bracket and positionally fix at least one helical filament |
US7122048B2 (en) | 2002-05-03 | 2006-10-17 | Scimed Life Systems, Inc. | Hypotube endoluminal device |
EP1503700B1 (en) | 2002-05-08 | 2012-09-26 | Abbott Laboratories | Endoprosthesis having foot extensions |
AU2003243204B2 (en) | 2002-05-16 | 2008-09-18 | Cook Medical Technologies Llc | Flexible barb for anchoring a prosthesis |
US7055612B2 (en) | 2002-05-17 | 2006-06-06 | The Viking Corporation | Fire protection system |
US6830638B2 (en) | 2002-05-24 | 2004-12-14 | Advanced Cardiovascular Systems, Inc. | Medical devices configured from deep drawn nickel-titanium alloys and nickel-titanium clad alloys and method of making the same |
US20040002752A1 (en) | 2002-06-26 | 2004-01-01 | Scimed Life Systems, Inc. | Sacrificial anode stent system |
US6761731B2 (en) | 2002-06-28 | 2004-07-13 | Cordis Corporation | Balloon-stent interaction to help reduce foreshortening |
ATE281800T1 (en) | 2002-09-09 | 2004-11-15 | Abbott Lab Vascular Entpr Ltd | SYSTEM FOR INSERTING A SELF-EXPANDING STENT |
US8444666B2 (en) | 2002-09-12 | 2013-05-21 | Cook Medical Technologies Llc | Retrievable filter |
US7001422B2 (en) | 2002-09-23 | 2006-02-21 | Cordis Neurovascular, Inc | Expandable stent and delivery system |
US7135038B1 (en) | 2002-09-30 | 2006-11-14 | Advanced Cardiovascular Systems, Inc. | Drug eluting stent |
US7169172B2 (en) | 2002-11-01 | 2007-01-30 | Counter Clockwise, Inc. | Method and apparatus for caged stent delivery |
US7169178B1 (en) | 2002-11-12 | 2007-01-30 | Advanced Cardiovascular Systems, Inc. | Stent with drug coating |
US6923829B2 (en) | 2002-11-25 | 2005-08-02 | Advanced Bio Prosthetic Surfaces, Ltd. | Implantable expandable medical devices having regions of differential mechanical properties and methods of making same |
US7678068B2 (en) | 2002-12-02 | 2010-03-16 | Gi Dynamics, Inc. | Atraumatic delivery devices |
US7044965B1 (en) | 2002-12-13 | 2006-05-16 | Spielberg Theodore E | Therapeutic cellular stent |
AU2003301005A1 (en) | 2002-12-16 | 2004-07-22 | The Regents Of The University Of Michigan | Assembly and planar structure for use therein which is expandable into a 3-d structure such as a stent and device for making the planar structure |
US20040147998A1 (en) | 2003-01-24 | 2004-07-29 | Nolting John E. | Differentially coated stent |
US7942920B2 (en) | 2003-02-25 | 2011-05-17 | Cordis Corporation | Stent with nested fingers for enhanced vessel coverage |
US8083791B2 (en) | 2003-04-14 | 2011-12-27 | Tryton Medical, Inc. | Method of treating a lumenal bifurcation |
US7591832B2 (en) | 2003-04-24 | 2009-09-22 | Medtronic, Inc. | Expandable guide sheath and apparatus with distal protection and methods for use |
KR100561713B1 (en) | 2003-05-23 | 2006-03-20 | (주) 태웅메디칼 | Flexible self-expandable stent and methods for making the stent |
US7112216B2 (en) * | 2003-05-28 | 2006-09-26 | Boston Scientific Scimed, Inc. | Stent with tapered flexibility |
US20040260377A1 (en) | 2003-06-17 | 2004-12-23 | Medinol, Ltd. | Shape memory alloy endoprosthesis delivery system |
US20040260384A1 (en) | 2003-06-17 | 2004-12-23 | Medtronic Ave | Superelastic coiled stent |
US6945990B2 (en) | 2003-08-16 | 2005-09-20 | Medtronic Vascular, Inc. | Double sheath deployment system |
US20050080479A1 (en) | 2003-09-29 | 2005-04-14 | Feng James Q. | Expandable endovascular stent |
US7060090B2 (en) | 2003-10-15 | 2006-06-13 | Medtronic Vascular, Inc. | Stent with increased longitudinal flexibility and scaffolding |
US20050090888A1 (en) | 2003-10-28 | 2005-04-28 | Hines Richard A. | Pleated stent assembly |
US7316711B2 (en) | 2003-10-29 | 2008-01-08 | Medtronic Vascular, Inc. | Intralumenal stent device for use in body lumens of various diameters |
US20050096725A1 (en) | 2003-10-29 | 2005-05-05 | Pomeranz Mark L. | Expandable stent having removable slat members |
US20050125025A1 (en) | 2003-12-05 | 2005-06-09 | Marcel Rioux | Styptic device |
US7873400B2 (en) | 2003-12-10 | 2011-01-18 | Stryker Leibinger Gmbh & Co. Kg. | Adapter for surgical navigation trackers |
US20050131530A1 (en) | 2003-12-15 | 2005-06-16 | Darack Ed E. | Endoluminal stent |
WO2005063251A1 (en) | 2003-12-17 | 2005-07-14 | Pfizer Products Inc. | Modified stent useful for delivery of drugs along stent strut |
US7243408B2 (en) | 2004-02-09 | 2007-07-17 | Boston Scientific Scimed, Inc. | Process method for attaching radio opaque markers to shape memory stent |
US7766960B2 (en) * | 2004-04-30 | 2010-08-03 | Novostent Corporation | Delivery catheter that controls foreshortening of ribbon-type prostheses and methods of making and use |
US7763064B2 (en) | 2004-06-08 | 2010-07-27 | Medinol, Ltd. | Stent having struts with reverse direction curvature |
JP2006029900A (en) | 2004-07-14 | 2006-02-02 | Tdk Corp | Magnetic sensor for encoder |
US8308789B2 (en) | 2004-07-16 | 2012-11-13 | W. L. Gore & Associates, Inc. | Deployment system for intraluminal devices |
US7323008B2 (en) | 2004-08-09 | 2008-01-29 | Medtronic Vascular, Inc. | Flexible stent |
US20060064155A1 (en) | 2004-09-01 | 2006-03-23 | Pst, Llc | Stent and method for manufacturing the stent |
US20060074480A1 (en) | 2004-09-01 | 2006-04-06 | Pst, Llc | Stent and method for manufacturing the stent |
US7018403B1 (en) | 2004-09-14 | 2006-03-28 | Advanced Cardiovascular Systems, Inc. | Inclined stent pattern for vulnerable plaque |
US7914570B2 (en) | 2004-10-07 | 2011-03-29 | Boston Scientific Scimed, Inc. | Non-shortening helical stent |
EP1819300B1 (en) | 2004-10-26 | 2012-07-04 | Cordis Corporation | Stent having phased hoop sections |
US20060173490A1 (en) | 2005-02-01 | 2006-08-03 | Boston Scientific Scimed, Inc. | Filter system and method |
US7918880B2 (en) | 2005-02-16 | 2011-04-05 | Boston Scientific Scimed, Inc. | Self-expanding stent and delivery system |
WO2006093976A1 (en) | 2005-02-28 | 2006-09-08 | Spirus Medical Inc. | Rotate-to-advance catheterization system |
US20070055365A1 (en) | 2005-04-28 | 2007-03-08 | The Cleveland Clinic Foundation | Stent with integrated filter |
US20070027522A1 (en) | 2005-06-14 | 2007-02-01 | Chang Jean C | Stent delivery and guidewire systems |
-
2006
- 2006-04-04 ES ES06740521T patent/ES2764992T3/en active Active
- 2006-04-04 CN CN200680011292.2A patent/CN101484089B/en active Active
- 2006-04-04 NZ NZ563119A patent/NZ563119A/en unknown
- 2006-04-04 EP EP19202499.0A patent/EP3613387B1/en active Active
- 2006-04-04 CN CN201110281152.XA patent/CN102302390B/en active Active
- 2006-04-04 JP JP2008505478A patent/JP5523700B2/en active Active
- 2006-04-04 US US11/397,987 patent/US7803180B2/en active Active
- 2006-04-04 EP EP06740521.7A patent/EP1871292B1/en active Active
- 2006-04-04 CN CN201110281185.4A patent/CN102309370B/en active Active
- 2006-04-04 EP EP12171358.0A patent/EP2505166B1/en active Active
- 2006-04-04 WO PCT/US2006/012579 patent/WO2006108010A2/en active Application Filing
- 2006-04-04 CA CA2610108A patent/CA2610108C/en active Active
- 2006-04-04 AU AU2006231559A patent/AU2006231559B2/en active Active
-
2007
- 2007-05-16 US US11/749,306 patent/US7556644B2/en active Active
-
2010
- 2010-09-17 US US12/884,514 patent/US20110029064A1/en not_active Abandoned
-
2012
- 2012-07-03 HK HK12106412.3A patent/HK1165257A1/en unknown
-
2014
- 2014-06-13 US US14/303,766 patent/US9592137B2/en active Active
Patent Citations (71)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5102417A (en) * | 1985-11-07 | 1992-04-07 | Expandable Grafts Partnership | Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft |
US5383892A (en) * | 1991-11-08 | 1995-01-24 | Meadox France | Stent for transluminal implantation |
US5749919A (en) * | 1994-01-10 | 1998-05-12 | Microfil Industries S.A. | Resilient prosthesis for widening a channel, particularly a blood vessel, and method for making same |
US5980552A (en) * | 1994-03-17 | 1999-11-09 | Medinol Ltd. | Articulated stent |
US5449373A (en) * | 1994-03-17 | 1995-09-12 | Medinol Ltd. | Articulated stent |
US5693085A (en) * | 1994-04-29 | 1997-12-02 | Scimed Life Systems, Inc. | Stent with collagen |
US5545210A (en) * | 1994-09-22 | 1996-08-13 | Advanced Coronary Technology, Inc. | Method of implanting a permanent shape memory alloy stent |
US20040088044A1 (en) * | 1995-03-01 | 2004-05-06 | Scimed Life Systems, 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 |
US6152957A (en) * | 1996-04-26 | 2000-11-28 | Jang; G. David | Intravascular stent |
US6039756A (en) * | 1996-04-26 | 2000-03-21 | Jang; G. David | Intravascular stent |
US5669932A (en) * | 1996-05-29 | 1997-09-23 | Isostent, Inc. | Means for accurately positioning an expandable stent |
US5755781A (en) * | 1996-08-06 | 1998-05-26 | Iowa-India Investments Company Limited | Embodiments of multiple interconnected stents |
US6146417A (en) * | 1996-08-22 | 2000-11-14 | Ischinger; Thomas | Tubular stent |
US7208009B2 (en) * | 1996-12-26 | 2007-04-24 | Medinol, Ltd. | Stent fabrication method |
US5810872A (en) * | 1997-03-14 | 1998-09-22 | Kanesaka; Nozomu | Flexible stent |
US7217286B2 (en) * | 1997-04-18 | 2007-05-15 | Cordis Corporation | Local delivery of rapamycin for treatment of proliferative sequelae associated with PTCA procedures, including delivery using a modified stent |
US6033433A (en) * | 1997-04-25 | 2000-03-07 | Scimed Life Systems, Inc. | Stent configurations including spirals |
US5824059A (en) * | 1997-08-05 | 1998-10-20 | Wijay; Bandula | Flexible stent |
US6231598B1 (en) * | 1997-09-24 | 2001-05-15 | Med Institute, Inc. | Radially expandable stent |
US6241762B1 (en) * | 1998-03-30 | 2001-06-05 | Conor Medsystems, Inc. | Expandable medical device with ductile hinges |
US6261319B1 (en) * | 1998-07-08 | 2001-07-17 | Scimed Life Systems, Inc. | Stent |
US6478816B2 (en) * | 1998-07-08 | 2002-11-12 | Scimed Life Systems, Inc. | Stent |
US6945993B2 (en) * | 1998-07-08 | 2005-09-20 | Boston Scientific Scimed, Inc. | Stent |
US5911754A (en) * | 1998-07-24 | 1999-06-15 | Uni-Cath Inc. | Flexible stent with effective strut and connector patterns |
US6949120B2 (en) * | 1998-10-23 | 2005-09-27 | Scimed Life Systems, Inc. | Helical stent design |
US6042597A (en) * | 1998-10-23 | 2000-03-28 | Scimed Life Systems, Inc. | Helical stent design |
US6488703B1 (en) * | 1998-10-23 | 2002-12-03 | Scimed Life Systems, Inc. | Helical stent design |
US20030050690A1 (en) * | 1998-10-23 | 2003-03-13 | Kveen Graig L. | Helical stent design |
US20050216076A1 (en) * | 1998-10-23 | 2005-09-29 | Boston Scientific Scimed, Inc. | Helical stent design |
US6632236B2 (en) * | 1999-03-12 | 2003-10-14 | Arteria Medical Science, Inc. | Catheter having radially expandable main body |
US6475237B2 (en) * | 1999-05-03 | 2002-11-05 | William J. Drasler | Intravascular hinge stent |
US6245101B1 (en) * | 1999-05-03 | 2001-06-12 | William J. Drasler | Intravascular hinge stent |
US6551351B2 (en) * | 1999-07-02 | 2003-04-22 | Scimed Life Systems | Spiral wound stent |
US6302907B1 (en) * | 1999-10-05 | 2001-10-16 | Scimed Life Systems, Inc. | Flexible endoluminal stent and process of manufacture |
US20030149473A1 (en) * | 1999-11-16 | 2003-08-07 | Chouinard Paul F. | Multi-section filamentary endoluminal stent |
US6585758B1 (en) * | 1999-11-16 | 2003-07-01 | Scimed Life Systems, Inc. | Multi-section filamentary endoluminal stent |
US20030114920A1 (en) * | 1999-12-21 | 2003-06-19 | Caro Colin Gerald | Vascular stents |
US20010039447A1 (en) * | 2000-03-01 | 2001-11-08 | Pinchasik Gregory A. | Longitudinally flexible stent |
US6352552B1 (en) * | 2000-05-02 | 2002-03-05 | Scion Cardio-Vascular, Inc. | Stent |
US6423091B1 (en) * | 2000-05-16 | 2002-07-23 | Cordis Corporation | Helical stent having flat ends |
US7169175B2 (en) * | 2000-05-22 | 2007-01-30 | Orbusneich Medical, Inc. | Self-expanding stent |
US20020082682A1 (en) * | 2000-12-19 | 2002-06-27 | Vascular Architects, Inc. | Biologically active agent delivery apparatus and method |
US20020095207A1 (en) * | 2001-01-15 | 2002-07-18 | Yousuke Moriuchi | Stent |
US6679911B2 (en) * | 2001-03-01 | 2004-01-20 | Cordis Corporation | Flexible stent |
US20020143390A1 (en) * | 2001-03-30 | 2002-10-03 | Tatsuzo Ishii | Stent |
US20030144729A1 (en) * | 2002-01-30 | 2003-07-31 | Scimed Life Systems, Inc. | Stent with wishbone connectors and serpentine bands |
US20030195609A1 (en) * | 2002-04-10 | 2003-10-16 | Scimed Life Systems, Inc. | Hybrid stent |
US20030204244A1 (en) * | 2002-04-26 | 2003-10-30 | Stiger Mark L. | Aneurysm exclusion stent |
US20040002753A1 (en) * | 2002-06-28 | 2004-01-01 | Robert Burgermeister | Stent with diagonal flexible connecting links |
US20040034402A1 (en) * | 2002-07-26 | 2004-02-19 | Syntheon, Llc | Helical stent having flexible transition zone |
US6969402B2 (en) * | 2002-07-26 | 2005-11-29 | Syntheon, Llc | Helical stent having flexible transition zone |
US6878162B2 (en) * | 2002-08-30 | 2005-04-12 | Edwards Lifesciences Ag | Helical stent having improved flexibility and expandability |
US20040172123A1 (en) * | 2002-12-20 | 2004-09-02 | Biotronik Gmbh & Co. Kg | Stent |
US20040122504A1 (en) * | 2002-12-24 | 2004-06-24 | Michael Hogendijk | Vascular prosthesis and methods of use |
US20050033410A1 (en) * | 2002-12-24 | 2005-02-10 | Novostent Corporation | Vascular prothesis having flexible configuration |
US20040186556A1 (en) * | 2002-12-24 | 2004-09-23 | Novostent Corporation | Vascular prosthesis and methods of use |
US7179286B2 (en) * | 2003-02-21 | 2007-02-20 | Boston Scientific Scimed, Inc. | Stent with stepped connectors |
US7131993B2 (en) * | 2003-06-25 | 2006-11-07 | Boston Scientific Scimed, Inc. | Varying circumferential spanned connectors in a stent |
US20060020322A1 (en) * | 2004-07-21 | 2006-01-26 | Alexander Leynov | Expandable framework with overlapping connectors |
US20060247759A1 (en) * | 2005-04-04 | 2006-11-02 | Janet Burpee | Flexible stent |
US20070208416A1 (en) * | 2005-04-04 | 2007-09-06 | Janet Burpee | Flexible stent |
US7803180B2 (en) * | 2005-04-04 | 2010-09-28 | Flexible Stenting Solutions, Inc. | Flexible stent |
US7556644B2 (en) * | 2005-04-04 | 2009-07-07 | Flexible Stenting Solutions, Inc. | Flexible stent |
US7637939B2 (en) * | 2005-06-30 | 2009-12-29 | Boston Scientific Scimed, Inc. | Hybrid stent |
US20070129786A1 (en) * | 2005-10-14 | 2007-06-07 | Bradley Beach | Helical stent |
US20090036976A1 (en) * | 2007-08-02 | 2009-02-05 | Bradley Beach | Flexible stent |
US7988723B2 (en) * | 2007-08-02 | 2011-08-02 | Flexible Stenting Solutions, Inc. | Flexible stent |
US20110245910A1 (en) * | 2007-08-02 | 2011-10-06 | Bradley Beach | Flexible stent |
US8500794B2 (en) * | 2007-08-02 | 2013-08-06 | Flexible Stenting Solutions, Inc. | Flexible stent |
US20100286760A1 (en) * | 2009-04-24 | 2010-11-11 | Bradley Beach | Flexible devices |
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US9980835B2 (en) | 2013-10-22 | 2018-05-29 | Orbusneich Medical Inc. | Medical device for implantation into luminal structures incorporating corrugated structural elements |
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JP5523700B2 (en) | 2014-06-18 |
CN102309370A (en) | 2012-01-11 |
ES2764992T3 (en) | 2020-06-05 |
AU2006231559A1 (en) | 2006-10-12 |
EP1871292A2 (en) | 2008-01-02 |
US9592137B2 (en) | 2017-03-14 |
EP1871292B1 (en) | 2019-10-23 |
US20060247759A1 (en) | 2006-11-02 |
WO2006108010A3 (en) | 2009-04-16 |
CN102309370B (en) | 2015-04-15 |
CN101484089B (en) | 2015-11-25 |
EP1871292A4 (en) | 2010-03-31 |
US20070208416A1 (en) | 2007-09-06 |
CA2610108A1 (en) | 2006-10-12 |
EP2505166A1 (en) | 2012-10-03 |
HK1165257A1 (en) | 2012-10-05 |
EP2505166B1 (en) | 2017-07-12 |
CN102302390A (en) | 2012-01-04 |
WO2006108010A2 (en) | 2006-10-12 |
CN102302390B (en) | 2016-05-25 |
US20140379066A1 (en) | 2014-12-25 |
NZ563119A (en) | 2011-02-25 |
JP2008544765A (en) | 2008-12-11 |
CN101484089A (en) | 2009-07-15 |
AU2006231559B2 (en) | 2012-03-22 |
EP3613387B1 (en) | 2023-01-11 |
EP3613387A1 (en) | 2020-02-26 |
US7803180B2 (en) | 2010-09-28 |
US7556644B2 (en) | 2009-07-07 |
CA2610108C (en) | 2014-03-25 |
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