US20010047200A1 - Non-foreshortening intraluminal prosthesis - Google Patents
Non-foreshortening intraluminal prosthesis Download PDFInfo
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- US20010047200A1 US20010047200A1 US09/416,994 US41699499A US2001047200A1 US 20010047200 A1 US20010047200 A1 US 20010047200A1 US 41699499 A US41699499 A US 41699499A US 2001047200 A1 US2001047200 A1 US 2001047200A1
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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
- A61F2/90—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
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- A—HUMAN NECESSITIES
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- 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
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- 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
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- 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
- A61F2002/91508—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 the meander having a difference in amplitude along the band
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- 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
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- 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
- A61F2002/91516—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 the meander having a change in frequency along the band
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- 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
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- 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
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- 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
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/91533—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other characterised by the phase between adjacent bands
- A61F2002/91541—Adjacent bands are arranged out of phase
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- A—HUMAN NECESSITIES
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- 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
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- 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
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- 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
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- 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
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Definitions
- the present invention relates to intraluminal prostheses for implantation into a mammalian vessel, and in particular, to intraluminal stents that do not experience foreshortening in the longitudinal direction when the stent is deployed to an expanded state.
- Intraluminal prosthesis such as stents
- stents are commonly used in the repair of aneurysms, as liners for vessels, or to provide mechanical support to prevent the collapse of stenosed or occluded vessels.
- These stents are typically delivered in a compressed state to a specific location inside the lumen of a vessel or other tubular structures, and then deployed at that location of the lumen to an expanded state.
- These stents have a diameter in their expanded state which is several times larger than the diameter of the stents in the compressed state.
- stents are also frequently deployed in the treatment of atherosclerotic stenosis in blood vessels, especially after percutaneous transluminal coronary angioplasty (PTCA) procedures, to improve the results of the procedure and to reduce the likelihood of restenosis.
- PTCA percutaneous transluminal coronary angioplasty
- U.S. Pat. Nos. 5,733,303 (Israel et al.) and 5,827,321 (Roubin et al.) describe the problems associated with the foreshortening of intraluminal stents when such stents are expanded.
- U.S. Pat. No. 5,733,303 (Israel et al.) describes stents that have struts whose longitudinal length decreases when the stent expands, thereby causing the overall longitudinal length of the stent to foreshorten. These struts are connected by flexible connecting members, each having an area of inflection that functions to compensate for the foreshortening experienced by the struts during expansion of the stent.
- a stent having a plurality of cells disposed about the circumference of the stent, with at least one cell having a plurality of struts that are connected together to form the cell. At least one strut has a portion that compensates for foreshortening of the struts during expansion of the stent.
- the present invention provides a stent having a plurality of cells disposed about the circumference of the stent, with at least one cell having a plurality of double-struts that are connected together to form the cell.
- the stent according to the present invention maintains a consistent length in both its fully compressed and fully expanded states, and in all states between its fully compressed and fully expanded states.
- the stent according to the present invention facilitates accurate sizing and deployment, thereby simplifying, and possibly reducing the time needed for, the medical procedure.
- FIG. 1 is a perspective view of a stent according to one embodiment of the present invention.
- FIG. 2A is a side elevational view of a portion of the stent of FIG. 1 in its expanded state
- FIG. 2B is a side elevational view of the portion of FIG. 2A in its compressed state
- FIG. 3A is an enlarged side elevational view of a cell of the portion of FIG. 2A;
- FIG. 3B illustrates the longitudinal component of a strut and its compensating portion of FIG. 3A when the stent is in its expanded state
- FIG. 3C illustrates the longitudinal component of a strut and its compensating portion of FIG. 3A when the stent is in its compressed state
- FIG. 4 illustrates a modification to the cell pattern of the stent of FIGS. 1 and 2A;
- FIG. 5 is an enlarged side elevational view of a cell of portion of a stent according to another embodiment of the present invention.
- FIG. 6A is a side elevational view of a portion of a stent according to another embodiment of the present invention.
- FIG. 6B is a side elevational view of the portion of FIG. 6A in its compressed state
- FIG. 6C illustrates the longitudinal component of a strut and its compensating portion of FIG. 6A when the stent is in its expanded state
- FIG. 6D illustrates the longitudinal component of a strut and its compensating portion of FIG. 6A when the stent is in its compressed state
- FIGS. 7 - 9 are side elevational views of portions of stents according to other embodiments of the present invention.
- FIG. 10 is an enlarged side elevational view of a cell of portion of a stent according to another embodiment of the present invention.
- FIGS. 11 - 14 are side elevational views of portions of stents according to other embodiments of the present invention.
- FIG. 15A is a side elevational view of a portions of a stent according to another embodiments of the present invention.
- FIG. 15B is a side elevational view of the portion of FIG. 15A in its compressed state.
- FIGS. 16 - 18 illustrate modifications to the cell pattern of the stent of FIG. 15.
- the intraluminal prosthesis according to the present invention is a stent, although the principles of the present invention are also applicable to other prosthesis such as liners and filters.
- the stent is delivered to a desired location in the lumen of a body vessel in a compressed state, and is then deployed by expanding it to its expanded state.
- the stent maintains substantially the same length in both its fully compressed and fully expanded states.
- the stent according to the present invention can be a self-expanding stent, or a stent that is radially expandable by inflating a balloon or expanded by an expansion member, or a stent that is expanded by the use of radio frequency which provides heat to cause the stent to change its size.
- the stent may also be coated with coverings of PTFE, dacron, or other biocompatible materials to form a combined stent-graft or endovascular prosthesis.
- the vessels in which the stent of the present invention can be deployed include but are not limited to natural body vessels such as ducts, arteries, trachea, veins, ureters and the esophagus, and artificial vessels such as grafts.
- FIGS. 1, 2A and 3 A A stent 20 according to the present invention is illustrated in FIGS. 1, 2A and 3 A in its expanded state.
- the stent 20 has a tubular configuration and is made up of a plurality of cells that are comprised of generally V-shaped struts connected at their apices.
- FIGS. 2A and 2B illustrate a portion of the stent 20 in greater detail, and
- FIG. 3A illustrates one cell 22 .
- Each cell 22 has a first strut 24 having a first end 26 and a second end 28 , a second strut 30 having a first end 32 and a second end 34 , a third strut 36 having a first end 38 and a second end 40 , and a fourth strut 42 having a first end 44 and a second end 46 .
- the first ends 26 and 32 of the first and second struts 24 and 30 are connected at a first apex 48
- the first ends 38 and 44 of the third and fourth struts 36 and 42 are connected at a second apex 50 .
- the second ends 28 and 40 of the first and third struts 24 and 36 , respectively, are connected to form a third apex 52
- the second ends 34 and 46 of the second and fourth struts 30 and 42 , respectively, are connected to form a fourth apex 54 , so that the four struts 24 , 30 , 36 and 42 together form an aperture or open space 56 .
- the first apex 48 of each cell 22 is connected to the second apex 50 of a longitudinally adjacent cell 22
- the third apex 52 of each cell 22 is connected to the fourth apex 54 of a transversely adjacent cell 22
- cells 22 can be provided in longitudinal rows and transverse columns. Therefore, the first and second apices 48 and 50 of adjacent cells 22 are connected to form a row R of cells 22 , while the third and fourth apices 52 and 54 of adjacent cells 22 are connected to form a column C of cells 22 .
- each compensating portion 60 has at least one point of inflection.
- the compensating portion 60 has three points of inflection 62 and 64 that are inflected in directions opposite to each other.
- One point of inflection 62 can be considered to be an external point of inflection since it extends outside the confines of the cell 22 as defined by the struts 24 , 30 , 36 and 42 .
- each of the other two points of inflection 64 can be considered to be an internal point of inflection since it extends into the aperture 56 .
- Each compensating portion 60 can be provided along any portion of the strut 36 and 42 , and slopes downwardly from one end of the strut 36 and 42 to an internal point of inflection 64 , at which point it slopes upwardly to the external point of inflection 62 , then slopes downwardly to the other internal point of inflection 64 , before sloping upwardly again towards the other end of the strut 36 or 42 .
- each compensating portion 60 has a plurality of alternating segments that are defined by the points of inflection 62 and 64 .
- the pattern of cells 22 can define a second pattern of cells 22 x that have about the same configuration as the cells 22 , but reversed about a vertical axis defined by apices 52 and 54 to form a substantial mirror image of the cells 22 .
- Each of the second cells 22 x is defined by a separate strut from four separate cells 22 .
- these second cells 22 x are also arranged to form rows and columns of cells 22 x.
- an internal point of inflection 64 of the third strut 36 can be nested or fitted inside the space defined by an external point of inflection 62 of the fourth strut 42
- an internal point of inflection 64 of the fourth strut 42 can nested or fitted inside the space defined by an external point of inflection 62 of the third strut 36 .
- FIG. 10 illustrates a cell 22 where each strut 24 , 30 , 36 and 42 has a compensating portion 60 .
- the compensating portions 60 function to compensate for the longitudinal foreshortening experienced by the struts 24 , 30 , 36 , 42 , thereby maintaining the stent 20 at substantially the same length at all times. This is accomplished by providing the compensating portions 60 with a natural bias and a springy nature, which together with its alternating segments, combine to shorten its length l 1 (see FIG. 3B) when compressed (i.e., 1 2 in FIG. 3C is less than l 1 ). When allowed to expand, each compensating portion 60 is biased to return to its natural or original position, which increases its length from l 2 to l 1 to compensate for the foreshortening experienced by the longitudinal component of each strut 24 , 30 , 36 , 42 .
- FIGS. 2A, 2B, 3 A, 3 B and 3 C This effect is illustrated in FIGS. 2A, 2B, 3 A, 3 B and 3 C.
- the compensating portion 60 When the stent 20 is in its compressed state, the compensating portion 60 has an actual length which is less than its actual length when the compensating portion 60 is in its expanded state.
- its alternating segments When the compensating portion 60 is in the compressed state, its alternating segments have a higher amplitude and a smaller wavelength than when it is in the expanded state (compare FIGS. 3B and 3C).
- this difference between the actual lengths of the compensating portion 60 in its two compressed and expanded states compensates for the difference between l 1 and l 2 of the struts 36 and 42 , so that the longitudinal lengths L 1 and L 2 of the strut (e.g., 36 ) are the same in both the compressed and expanded states.
- the lines 70 and 72 in FIGS. 2A and 2B also show that the relevant portion of the stent 20 does not experience any foreshortening.
- FIG. 4 illustrates a modification to the cell pattern for stent 20 shown in FIG. 2A.
- the cell pattern 20 a in FIG. 4 provides a plurality of straight connecting members 80 that connect the first and second apices 48 and 50 , respectively, of adjacent cells 22 in a longitudinal row R.
- These straight connecting members 80 can increase the flexibility of the stent, primarily in the longitudinal direction, but also to a small degree in the radial direction.
- one or more of these straight connecting members 80 can be omitted, either randomly or in a pattern (e.g., in a spiral pattern) to increase the flexibility of the stent at desired locations.
- the compensating portions 60 have been described in FIGS. 1 - 3 as assuming a particular configuration, it will be appreciated by those skilled in the art that the compensating portions 60 can assume other configurations without departing from the spirit and scope of the present invention.
- the compensating portion 60 can be modified so that each has two points of inflection. This is illustrated in FIG. 5, where the third strut 36 has a compensating portion 60 a that has one external point of inflection 62 a and one internal point of inflection 64 a, and the fourth strut 42 has a compensating portion 60 a that has one external point of inflection 62 a and one internal point of inflection 64 a.
- FIGS. 6 - 9 illustrate another type of compensating portion 90 according to the present invention which is configured to be a generally incomplete or C-shaped circle provided at one or more apices of the cells.
- each cell 22 b is essentially the same as cell 22 in FIG. 3A, except that the compensating portions 60 have been replaced by compensating portions 90 b that are provided at the location of the first and second apices 48 and 50 in such a manner that the first and second apices 48 and 50 are replaced by these compensating portions 90 b.
- Each compensating portion 90 b has a generally incomplete circular or C-shaped configuration, extending from the first end 26 b, 32 b, 38 b or 44 b of one of the struts 24 b, 32 b, 36 b or 42 b, respectively, then curling around in a circular fashion to the first end 26 b, 32 b, 38 b or 44 b of the adjacent strut 24 b, 32 b, 36 b or 42 b, respectively.
- the elements of the cell 22 b that are the same as the elements of the cell 22 in FIG. 3A are provided with the same numeral designations except that a “b” has been added to the numeral designations in FIG. 6A.
- Each compensating portion 90 b of each cell 22 b is longitudinally (i.e., along a row) connected to a compensating portion 90 b of an adjacent cell 22 b by a straight connecting member 80 b.
- the compensating portions 90 b function in the same manner as the compensating portions 60 to compensate for the longitudinal foreshortening experienced by the struts 24 b, 30 b, 36 b, 42 b.
- each compensating portion 90 b has one area of inflection 95 so that each compensating portion 90 b has a shortened longitudinal length L 2 when compressed, but has an increased longitudinal length L 1 when allowed to expand so as to compensate for the foreshortening experienced by the longitudinal component of each strut 24 b, 30 b, 36 b, 42 b.
- This effect is illustrated in FIGS. 6B, 6C and 6 D.
- FIG. 7 illustrates a stent pattern in which each cell 22 c is essentially the same as cell 22 b in FIG. 6A, except that the compensating portions 90 c are now provided at the third and fourth apices 52 and 54 , respectively, in such a manner that the third and fourth apices 52 and 54 are replaced by these compensating portions 90 c.
- Each compensating portion 90 c has the same configuration as compensating portion 90 b.
- the elements of the cell 22 c that are the same as the elements of the cell 22 b in FIG. 6A are provided with the same numeral designations except that a “c” has been added to the numeral designations in FIG. 7.
- Each compensating portion 90 c of each cell 22 c can be transversely (i.e., along a column) connected to a compensating portion 90 c of an adjacent cell 22 c by a straight connecting member 80 c.
- FIG. 8 illustrates a stent pattern in which each cell 22 d has compensating portions 90 d provided at all four apieces 48 , 50 , 52 and 54 , in such a manner that each of the four apieces 48 , 50 , 52 and 54 is replaced by a compensating portion 90 d.
- Each compensating portion 90 d of each cell 22 d can be either longitudinally or transversely connected to a compensating portion 90 d of an adjacent cell 22 d by a straight connecting member 80 d.
- the elements of the cell 22 d that are the same as the elements of the cells 22 b and 22 c are provided with the same numeral designations except that a “d” has been added to the numeral designations in FIG. 8.
- FIG. 9 illustrates a stent pattern which is the same as the stent pattern in FIG. 8, except that the connecting members 80 d are omitted.
- each compensating portion 90 e of each cell 22 e in FIG. 9 is directly connected, either longitudinally or transversely, to a compensating portion 90 e of an adjacent cell 22 e.
- the elements of the cell 22 e that are the same as the elements of the cell 22 d are provided with the same numeral designations except that an “e” has been added to the numeral designations in FIG. 9.
- FIGS. 11 and 12 illustrate different types of compensating portions according to the present invention that embody the underlying principles described in connection with FIGS. 6 - 9 .
- each cell 22 g shares a compensating portion 90 g with each longitudinally adjacent cell 22 g.
- each compensating portion 90 g is shaped like a sideway “S”, with the top of the “S” coupled to a first cell 22 g at the location of (and replacing) the first apex 48 , and with the bottom of the “S” coupled to a longitudinally adjacent second cell 22 g at the location of (and replacing) the second apex 50 of the second cell 22 g.
- each compensating portion 90 g defines two areas of inflection 100 and 102 that function to provide the compensation needed to avoid foreshortening according to the principles set forth in FIGS. 2 - 9 above. Otherwise, the elements of the cell 22 g in FIG. 11 that are the same as the elements of the cell 22 in FIG. 3A are provided with the same numeral designations except that a “g” has been added to the numeral designations in FIG. 11.
- each cell 22 h shares a compensating portion 90 h with each longitudinally adjacent cell 22 h.
- each compensating portion 90 h is configured like the compensating portion 90 b in FIG. 6, except that a first end 106 of the compensating portion 90 h is connected to the first end 44 h of the fourth strut 42 h of a first cell 22 h, with the compensating portion 90 h curling around in a circular fashion to its second end 108 , which is connected to the first end 32 h of the second strut 30 h of a longitudinally adjacent second cell 22 h.
- the first end 38 h of the third strut 36 h of the first cell 22 h is connected to the compensating portion 90 h between the first and second ends 106 and 108 thereof, and the first end 26 h of the first strut 24 h of the second cell 22 h is connected to the compensating portion 90 h between the second end 108 and the first end 38 h of the third strut 36 h of the first cell 22 h.
- the compensating portion 90 h defines one area of inflection 110 between two longitudinally adjacent cells 22 h that functions to provide the compensation needed to avoid foreshortening according to the principles set forth in FIGS. 2 - 9 above.
- the elements of the cell 22 h in FIG. 12 that are the same as the elements of the cell 22 in FIG. 3A are provided with the same numeral designations except that an “h” has been added to the numeral designations in FIG. 12.
- FIG. 13 illustrates a stent pattern in which the cells 22 i are essentially the same as the cell 22 in FIG. 3A, except that each strut 24 i, 30 i, 36 i and 42 i is now completely curved. Otherwise, the elements of the cell 22 i in FIG. 13 that are the same as the elements of the cell 22 in FIG. 3A are provided with the same numeral designations except that an “i” has been added to the numeral designations in FIG. 13.
- the cells 22 j in the stent pattern in FIG. 14 borrow from the principles illustrated in FIGS. 3A and 13.
- Each strut in the cells 22 j are made up of two strut pieces that have their respective ends connected at the apices 48 j, 50 j, 52 j and 54 j.
- first strut 24 j has an accompanying inner strut piece 24 k whose ends are also connected to the apices 48 j and 52 j
- second strut 30 j has an accompanying inner strut piece 30 k whose ends are also connected to the apices 48 j and 54 j
- third strut 36 j has an accompanying inner strut piece 36 k whose ends are also connected to the apices 50 j and 52 j
- fourth strut 42 j has an accompanying inner strut piece 42 k whose ends are also connected to the apices 50 j and 54 j.
- Each strut 24 j, 30 j, 36 j, 42 j and its accompanying inner strut piece 24 k, 30 k, 36 k, 42 k defines a smaller cell 120 , 122 , 124 , 126 , respectively.
- the inner strut pieces 24 k, 30 k, 36 k, 42 k are shorter than each corresponding strut 24 j, 30 j, 36 j, 42 j.
- the double-strut structure may increase the strength of the stent by providing radial and longitudinal resistance to compression and other changes in shape.
- the resulting stent may have an increased expansion ratio.
- the double-strut structure may reduce the tendency of the stent to recoil.
- the resulting stent may have increased stent coverage and cells that have smaller sizes, thereby minimizing tissue in-growth.
- the double-strut embodiment of FIG. 14 can be especially useful in applications where the prosthesis requires increased support throughout the prosthesis while minimizing the potential for stent kink or breakage at certain regions along the stent.
- FIG. 15A illustrates a stent 20 m in which the cells 22 m are essentially the same as the cell 22 i in FIG. 13, except that each strut 24 m, 30 m, 36 m and 42 m has less curvature. In fact, each strut 24 m, 30 m, 36 m and 42 m has one internal point of inflection 64 m and one external point of inflection 62 m. Otherwise, the elements of the cell 22 m in FIG. 15 that are the same as the elements of the cell 22 i in FIG. 13 are provided with the same numeral designations except that an “m” has been added to the numeral designations in FIG. 15. Similar to FIG.
- the pattern of cells 22 m can define a second pattern of cells 22 y that have about the same configuration as the cells 22 m, but reversed about a horizontal axis defined by the apices 48 m and 50 m. Like the cells 22 m, these second cells 22 y are also arranged to form rows and columns of cells 22 y. Each of the second cells 22 y is defined by a separate strut from four separate cells 22 m.
- FIG. 15B illustrates the stent 20 m in the compressed state.
- One difference between the cell 22 m and the other cells 22 herein is that the apex 54 m in each cell 22 m is inverted internally into the cell 22 m, as opposed to extending externally from the cell 22 m.
- FIGS. 16 - 18 illustrate stent patterns that are made up entirely of cells 22 that have compensating portions 60
- FIGS. 16 - 18 These principles will be illustrated in FIGS. 16 - 18 using the cell pattern 22 m of FIG. 15.
- a stent 20 m is illustrated as having a central portion 150 made up of a plurality of conventional zig-zag struts that do not have any compensating portions, and which form diamond-shaped cells 152 .
- the two ends of the stent 20 m is made up of the cell pattern 22 m illustrated in FIG. 15.
- This configuration provides more rigidity in the central portion 150 , and is better suited for use, for example, in the carotid arteries where more calcified lesions can be found at about the central portion 150 , and where there is more potential for embolization in the central portion 150 . This is because the diamond-shaped cells 152 are better suited to minimize embolization and prevent tissue in-growth.
- FIG. 17 illustrates a stent 20 n having a first portion 154 made up of a plurality of conventional zig-zag struts that do not have any compensating portions, and which form diamond-shaped cells 152 , and a second portion 156 that is made up of the cell pattern 22 m illustrated in FIG. 15.
- the first portion 154 can be used to support a body vessel at a location that requires more rigidity
- the second portion 156 can be used to support a body vessel at a location that requires more flexibility.
- This configuration is better suited for use, for example, in the iliac arteries where the origin of the iliac arteries might have more calcified lesions where the first portion 154 would be intended to support.
- FIG. 18 illustrates a stent 20 p having rows 158 of cells 22 m separated by one or more rows of the diamond-shaped cells 152 .
- the rows 158 can be individual rows of cells 22 m, or a plurality of rows of cells 22 m. This configuration is useful in distributing the radial strength of the stent 20 p while allowing for nonforeshortening and increased flexion at the desired locations (i.e., supported by the cells 22 m ). This configuration is best suited for use, for example, with curved vessels such as external iliac arteries.
- a number of materials can be used to fabricate the stent 20 (including its struts 24 , 30 , 36 , 42 and connecting members 80 ), depending on its method of deployment. These materials include, but are not limited to, Nitinol (which is a shape memory superelastic metal alloy whose use in stents is well-documented in the literature), stainless steel, tantalum, titanium, elgiloy, gold, platinum, or any other metal or alloy, or polymers or composites, having sufficient biocompatibility, rigidity, flexibility, radial strength, radiopacity and antithrombogenicity.
- Nitinol which is a shape memory superelastic metal alloy whose use in stents is well-documented in the literature
- stainless steel tantalum, titanium, elgiloy, gold, platinum, or any other metal or alloy, or polymers or composites, having sufficient biocompatibility, rigidity, flexibility, radial strength, radiopacity and antithrombogenicity.
- the stent 20 can be made from one of a number of methods, depending on the material of the stent 20 and the desired nature of deployment.
- the stent 20 is fabricated from a solid Nitinol tube with dimensions that are identical to the stent 20 when it is in the fully compressed state.
- the pattern of the stent 20 i.e., its cells 22
- a computer-guided laser cutter which cuts out the segments between the struts and the connecting members (if any) in a manner which closely maintains the outside diameter and wall thickness of the stent 20 .
- the stent 20 is progressively expanded until it reaches its fully expanded state.
- the expansion can be performed by an internal expansion fixture, although other expansion apparatus and methods can be used without departing from the spirit and scope of the present invention.
- the overall length of the stent 20 must be consistently maintained throughout the expansion of the stent 20 from its fully compressed to its fully expanded states.
- the stent 20 Once the stent 20 has been expanded to its fully expanded state, it is heat-treated to “set” the shape memory of the Nitinol material so that it will fully return to its expanded dimensions at a temperature that is near body temperature. The stent 20 is then cleaned and electro-polished.
- the next step is to compress the stent 20 again into a dimension which allows for delivery into a vessel, either through percutaneous delivery or through minimally invasive surgical procedures.
- the stent 20 must be compressed into a smaller state so that it can be delivered by a delivery device to the desired location of the vessel. Any conventional delivery device could be used, such as but not limited to a tube, catheter, or sheath.
- This compression is accomplished by cooling the stent 20 to a low temperature, for example, zero degrees Celcius, and while maintaining this temperature, compressing the stent 20 to allow the stent 20 to be inserted inside the delivery device.
- the stent 20 is held by the delivery device in the compressed state until it is released within the lumen of a vessel, at which time the stent will fully re-expand to its “set” dimensions as it equilibrates with body temperature.
- a balloon-expandable stent 20 can be fabricated by connecting a plurality of wires that have been bent or formed into the desired shapes for the struts 24 , 30 , 36 , 42 and connecting members 80 .
- the connection can be accomplished by welding, tying, bonding, or any other conventional method.
- wire electro-discharge machining or a computer guided laser cutter can be used.
- the wires are capable of experiencing plastic deformation when the stent 20 is compressed, and when the stent 20 is expanded. Upon plastic deformation of the stent 20 to either the compressed or the expanded state, the stent 20 remains in this state until another force is applied to plastically deform the stent 20 again.
- the stent 20 can be deployed by a number of delivery systems and delivery methods. These delivery systems and methods will vary depending on whether the stent 20 is expanded by self-expansion, radial expansion forces, or radio frequency. These delivery methods are well-known in the art, and shall not be described in greater detail herein.
- the present invention provides a stent having struts that include portions that compensate for the foreshortening effect.
- connecting members can be omitted from the stent designs according to the present invention, leading to at least the following benefits.
- cell sizes can be decreased so as to minimize “in-stent restenosis”, and to provide better support to the vessel.
- the stent can be provided with a more uniform structure that distributes any angulation or flexion of the stent more evenly along the full length of the stent, so that the stent can experience a more gradual curvature at bends rather than experiencing undesirable kinking at such regions. This further minimizes breakage or other damage to the stent.
- connecting members can be optionally added to increase the flexibility of the stent at certain desired areas.
Abstract
A stent has a plurality of cells disposed about the circumference of the stent, with at least one cell having a plurality of struts that are connected together to form the cell. At least one strut has a portion that compensates for foreshortening of the struts during expansion of the stent.
Description
- 1. Field of the Invention
- The present invention relates to intraluminal prostheses for implantation into a mammalian vessel, and in particular, to intraluminal stents that do not experience foreshortening in the longitudinal direction when the stent is deployed to an expanded state.
- 2. Description of the Prior Art
- Intraluminal prosthesis, such as stents, are commonly used in the repair of aneurysms, as liners for vessels, or to provide mechanical support to prevent the collapse of stenosed or occluded vessels. These stents are typically delivered in a compressed state to a specific location inside the lumen of a vessel or other tubular structures, and then deployed at that location of the lumen to an expanded state. These stents have a diameter in their expanded state which is several times larger than the diameter of the stents in the compressed state. These stents are also frequently deployed in the treatment of atherosclerotic stenosis in blood vessels, especially after percutaneous transluminal coronary angioplasty (PTCA) procedures, to improve the results of the procedure and to reduce the likelihood of restenosis.
- U.S. Pat. Nos. 5,733,303 (Israel et al.) and 5,827,321 (Roubin et al.) describe the problems associated with the foreshortening of intraluminal stents when such stents are expanded. In addition, U.S. Pat. No. 5,733,303 (Israel et al.) describes stents that have struts whose longitudinal length decreases when the stent expands, thereby causing the overall longitudinal length of the stent to foreshorten. These struts are connected by flexible connecting members, each having an area of inflection that functions to compensate for the foreshortening experienced by the struts during expansion of the stent.
- Unfortunately, there are certain drawbacks associated with providing flexible connecting members that have areas of inflection. First, to accommodate the areas of inflection, these connecting members often create segments within the stent where the aperture or opening defined by these connecting members have a large size. Such increased aperture size may allow increased ingrowth of tissue (also known as “in-stent restenosis”). Second, curved areas of inflection on these connecting members may cause distortion of the lumen of the stent when the stent is twisted or experiences angulation in the longitudinal direction. Third, the connecting members form an area of weakness in the stent structure which may encourage kink of the stent at the site with flexion or angulation, or which in extreme circumstances may lead to stent breakage after experiencing repetitive stress. In other words, the provision of the connecting members decreases the amount of support that the stent can enjoy.
- Thus, there still remains a need for an intraluminal prosthesis that maintains a consistent length in both its fully compressed and fully expanded states, while avoiding the disadvantages set forth above. There also remains a need for a stent which can accommodate body vessels having varying lumen diameters, different anatomies, and different disease states.
- It is an object of the present invention to provide an intraluminal prosthesis that maintains a consistent length in both its fully compressed and fully expanded states.
- It is another object of the present invention to provide an intraluminal prosthesis that provides increased support throughout the prosthesis while minimizing the potential for stent kink or breakage at certain regions along the stent.
- It is yet another object of the present invention to provide an intraluminal prosthesis that minimizes the potential for in-stent restenosis.
- In order to accomplish the objects of the present invention, there is provided a stent having a plurality of cells disposed about the circumference of the stent, with at least one cell having a plurality of struts that are connected together to form the cell. At least one strut has a portion that compensates for foreshortening of the struts during expansion of the stent.
- In another embodiment, the present invention provides a stent having a plurality of cells disposed about the circumference of the stent, with at least one cell having a plurality of double-struts that are connected together to form the cell.
- Thus, the stent according to the present invention maintains a consistent length in both its fully compressed and fully expanded states, and in all states between its fully compressed and fully expanded states. As a result, the stent according to the present invention facilitates accurate sizing and deployment, thereby simplifying, and possibly reducing the time needed for, the medical procedure.
- FIG. 1 is a perspective view of a stent according to one embodiment of the present invention;
- FIG. 2A is a side elevational view of a portion of the stent of FIG. 1 in its expanded state;
- FIG. 2B is a side elevational view of the portion of FIG. 2A in its compressed state;
- FIG. 3A is an enlarged side elevational view of a cell of the portion of FIG. 2A;
- FIG. 3B illustrates the longitudinal component of a strut and its compensating portion of FIG. 3A when the stent is in its expanded state;
- FIG. 3C illustrates the longitudinal component of a strut and its compensating portion of FIG. 3A when the stent is in its compressed state;
- FIG. 4 illustrates a modification to the cell pattern of the stent of FIGS. 1 and 2A;
- FIG. 5 is an enlarged side elevational view of a cell of portion of a stent according to another embodiment of the present invention;
- FIG. 6A is a side elevational view of a portion of a stent according to another embodiment of the present invention;
- FIG. 6B is a side elevational view of the portion of FIG. 6A in its compressed state;
- FIG. 6C illustrates the longitudinal component of a strut and its compensating portion of FIG. 6A when the stent is in its expanded state;
- FIG. 6D illustrates the longitudinal component of a strut and its compensating portion of FIG. 6A when the stent is in its compressed state;
- FIGS.7-9 are side elevational views of portions of stents according to other embodiments of the present invention;
- FIG. 10 is an enlarged side elevational view of a cell of portion of a stent according to another embodiment of the present invention;
- FIGS.11-14 are side elevational views of portions of stents according to other embodiments of the present invention; and
- FIG. 15A is a side elevational view of a portions of a stent according to another embodiments of the present invention;
- FIG. 15B is a side elevational view of the portion of FIG. 15A in its compressed state; and
- FIGS.16-18 illustrate modifications to the cell pattern of the stent of FIG. 15.
- The following detailed description is of the best presently contemplated modes of carrying out the invention. This description is not to be taken in a limiting sense, but is made merely for the purpose of illustrating general principles of embodiments of the invention. The scope of the invention is best defined by the appended claims.
- The intraluminal prosthesis according to the present invention is a stent, although the principles of the present invention are also applicable to other prosthesis such as liners and filters. The stent is delivered to a desired location in the lumen of a body vessel in a compressed state, and is then deployed by expanding it to its expanded state. The stent maintains substantially the same length in both its fully compressed and fully expanded states.
- The stent according to the present invention can be a self-expanding stent, or a stent that is radially expandable by inflating a balloon or expanded by an expansion member, or a stent that is expanded by the use of radio frequency which provides heat to cause the stent to change its size. The stent may also be coated with coverings of PTFE, dacron, or other biocompatible materials to form a combined stent-graft or endovascular prosthesis. The vessels in which the stent of the present invention can be deployed include but are not limited to natural body vessels such as ducts, arteries, trachea, veins, ureters and the esophagus, and artificial vessels such as grafts.
- A stent20 according to the present invention is illustrated in FIGS. 1, 2A and 3A in its expanded state. Referring to FIG. 1, the stent 20 has a tubular configuration and is made up of a plurality of cells that are comprised of generally V-shaped struts connected at their apices. FIGS. 2A and 2B illustrate a portion of the stent 20 in greater detail, and FIG. 3A illustrates one
cell 22. Eachcell 22 has afirst strut 24 having afirst end 26 and asecond end 28, asecond strut 30 having afirst end 32 and asecond end 34, athird strut 36 having afirst end 38 and asecond end 40, and afourth strut 42 having afirst end 44 and asecond end 46. The first ends 26 and 32 of the first andsecond struts first apex 48, and the first ends 38 and 44 of the third andfourth struts second apex 50. The second ends 28 and 40 of the first andthird struts third apex 52, and the second ends 34 and 46 of the second andfourth struts fourth apex 54, so that the four struts 24, 30, 36 and 42 together form an aperture oropen space 56. - As shown in FIG. 2A, the
first apex 48 of eachcell 22 is connected to thesecond apex 50 of a longitudinallyadjacent cell 22, and thethird apex 52 of eachcell 22 is connected to thefourth apex 54 of a transverselyadjacent cell 22. For purposes of the present invention,cells 22 can be provided in longitudinal rows and transverse columns. Therefore, the first andsecond apices adjacent cells 22 are connected to form a row R ofcells 22, while the third andfourth apices adjacent cells 22 are connected to form a column C ofcells 22. - The
struts struts portion 60 that functions to compensate for the foreshortening experienced by thestruts portion 60 has at least one point of inflection. In the non-limiting example shown in FIG. 3A, the compensatingportion 60 has three points ofinflection inflection 62 can be considered to be an external point of inflection since it extends outside the confines of thecell 22 as defined by thestruts inflection 64 can be considered to be an internal point of inflection since it extends into theaperture 56. Each compensatingportion 60 can be provided along any portion of thestrut strut inflection 64, at which point it slopes upwardly to the external point ofinflection 62, then slopes downwardly to the other internal point ofinflection 64, before sloping upwardly again towards the other end of thestrut portion 60 has a plurality of alternating segments that are defined by the points ofinflection - As best shown in FIG. 2A, the pattern of
cells 22 can define a second pattern ofcells 22 x that have about the same configuration as thecells 22, but reversed about a vertical axis defined byapices cells 22. Each of thesecond cells 22 x is defined by a separate strut from fourseparate cells 22. Like thecells 22, thesesecond cells 22 x are also arranged to form rows and columns ofcells 22 x. - Referring to FIG. 2B, when the stent20 is in the compressed state, the internal points of
inflection 64 are adjacent to each other. However, it is possible to position the compensatingportions 60 along the third andfourth struts inflection inflection 64 of thethird strut 36 can be nested or fitted inside the space defined by an external point ofinflection 62 of thefourth strut 42, and an internal point ofinflection 64 of thefourth strut 42 can nested or fitted inside the space defined by an external point ofinflection 62 of thethird strut 36. - As another example, it is possible to also provide the compensating
portions 60 for the first andsecond struts portions 60 for the third andfourth struts cell 22 where eachstrut portion 60. - The compensating
portions 60 function to compensate for the longitudinal foreshortening experienced by thestruts portions 60 with a natural bias and a springy nature, which together with its alternating segments, combine to shorten its length l1 (see FIG. 3B) when compressed (i.e., 1 2 in FIG. 3C is less than l1). When allowed to expand, each compensatingportion 60 is biased to return to its natural or original position, which increases its length from l2 to l1 to compensate for the foreshortening experienced by the longitudinal component of eachstrut - This effect is illustrated in FIGS. 2A, 2B,3A, 3B and 3C. When the stent 20 is in its compressed state, the compensating
portion 60 has an actual length which is less than its actual length when the compensatingportion 60 is in its expanded state. When the compensatingportion 60 is in the compressed state, its alternating segments have a higher amplitude and a smaller wavelength than when it is in the expanded state (compare FIGS. 3B and 3C). Thus, this difference between the actual lengths of the compensatingportion 60 in its two compressed and expanded states compensates for the difference between l1 and l2 of thestruts - FIG. 4 illustrates a modification to the cell pattern for stent20 shown in FIG. 2A. In particular, the cell pattern 20 a in FIG. 4 provides a plurality of straight connecting
members 80 that connect the first andsecond apices adjacent cells 22 in a longitudinal row R. These straight connectingmembers 80 can increase the flexibility of the stent, primarily in the longitudinal direction, but also to a small degree in the radial direction. In addition, one or more of these straight connectingmembers 80 can be omitted, either randomly or in a pattern (e.g., in a spiral pattern) to increase the flexibility of the stent at desired locations. - Although the compensating
portions 60 have been described in FIGS. 1-3 as assuming a particular configuration, it will be appreciated by those skilled in the art that the compensatingportions 60 can assume other configurations without departing from the spirit and scope of the present invention. For example, the compensatingportion 60 can be modified so that each has two points of inflection. This is illustrated in FIG. 5, where thethird strut 36 has a compensatingportion 60 a that has one external point of inflection 62 a and one internal point ofinflection 64 a, and thefourth strut 42 has a compensatingportion 60 a that has one external point of inflection 62 a and one internal point ofinflection 64 a. - FIGS.6-9 illustrate another type of compensating
portion 90 according to the present invention which is configured to be a generally incomplete or C-shaped circle provided at one or more apices of the cells. For example, referring to FIG. 6A, each cell 22 b is essentially the same ascell 22 in FIG. 3A, except that the compensatingportions 60 have been replaced by compensatingportions 90 b that are provided at the location of the first andsecond apices second apices portions 90 b. Each compensatingportion 90 b has a generally incomplete circular or C-shaped configuration, extending from thefirst end struts 24 b, 32 b, 36 b or 42 b, respectively, then curling around in a circular fashion to thefirst end adjacent strut 24 b, 32 b, 36 b or 42 b, respectively. The elements of the cell 22 b that are the same as the elements of thecell 22 in FIG. 3A are provided with the same numeral designations except that a “b” has been added to the numeral designations in FIG. 6A. - Each compensating
portion 90 b of each cell 22 b is longitudinally (i.e., along a row) connected to a compensatingportion 90 b of an adjacent cell 22 b by a straight connecting member 80 b. The compensatingportions 90 b function in the same manner as the compensatingportions 60 to compensate for the longitudinal foreshortening experienced by thestruts 24 b, 30 b, 36 b, 42 b. In this regard, the generally circular curved configuration of the compensatingportions 90 b has one area of inflection 95 so that each compensatingportion 90 b has a shortened longitudinal length L2 when compressed, but has an increased longitudinal length L1 when allowed to expand so as to compensate for the foreshortening experienced by the longitudinal component of eachstrut 24 b, 30 b, 36 b, 42 b. This effect is illustrated in FIGS. 6B, 6C and 6D. - FIG. 7 illustrates a stent pattern in which each cell22 c is essentially the same as cell 22 b in FIG. 6A, except that the compensating portions 90 c are now provided at the third and
fourth apices fourth apices portion 90 b. The elements of the cell 22 c that are the same as the elements of the cell 22 b in FIG. 6A are provided with the same numeral designations except that a “c” has been added to the numeral designations in FIG. 7. Each compensating portion 90 c of each cell 22 c can be transversely (i.e., along a column) connected to a compensating portion 90 c of an adjacent cell 22 c by a straight connecting member 80 c. - The principles illustrated in FIGS. 6A and 7 can be combined. For example, FIG. 8 illustrates a stent pattern in which each
cell 22 d has compensating portions 90 d provided at all fourapieces apieces cell 22 d can be either longitudinally or transversely connected to a compensating portion 90 d of anadjacent cell 22 d by a straight connecting member 80 d. The elements of thecell 22 d that are the same as the elements of the cells 22 b and 22 c are provided with the same numeral designations except that a “d” has been added to the numeral designations in FIG. 8. - In addition, FIG. 9 illustrates a stent pattern which is the same as the stent pattern in FIG. 8, except that the connecting members80 d are omitted. Thus, each compensating
portion 90 e of eachcell 22 e in FIG. 9 is directly connected, either longitudinally or transversely, to a compensatingportion 90 e of anadjacent cell 22 e. The elements of thecell 22 e that are the same as the elements of thecell 22 d are provided with the same numeral designations except that an “e” has been added to the numeral designations in FIG. 9. - FIGS. 11 and 12 illustrate different types of compensating portions according to the present invention that embody the underlying principles described in connection with FIGS.6-9. In FIG. 11, each cell 22 g shares a compensating portion 90 g with each longitudinally adjacent cell 22 g. In particular, each compensating portion 90 g is shaped like a sideway “S”, with the top of the “S” coupled to a first cell 22 g at the location of (and replacing) the
first apex 48, and with the bottom of the “S” coupled to a longitudinally adjacent second cell 22 g at the location of (and replacing) thesecond apex 50 of the second cell 22 g. Thus, the sideway “S” shape of each compensating portion 90 g defines two areas ofinflection cell 22 in FIG. 3A are provided with the same numeral designations except that a “g” has been added to the numeral designations in FIG. 11. - Similarly, in FIG. 12, each
cell 22 h shares a compensatingportion 90 h with each longitudinallyadjacent cell 22 h. In particular, each compensatingportion 90 h is configured like the compensatingportion 90 b in FIG. 6, except that afirst end 106 of the compensatingportion 90 h is connected to the first end 44 h of thefourth strut 42 h of afirst cell 22 h, with the compensatingportion 90 h curling around in a circular fashion to itssecond end 108, which is connected to thefirst end 32 h of thesecond strut 30 h of a longitudinally adjacentsecond cell 22 h. Thefirst end 38 h of the third strut 36 h of thefirst cell 22 h is connected to the compensatingportion 90 h between the first and second ends 106 and 108 thereof, and thefirst end 26 h of thefirst strut 24 h of thesecond cell 22 h is connected to the compensatingportion 90 h between thesecond end 108 and thefirst end 38 h of the third strut 36 h of thefirst cell 22 h. Thus, the compensatingportion 90 h defines one area ofinflection 110 between two longitudinallyadjacent cells 22 h that functions to provide the compensation needed to avoid foreshortening according to the principles set forth in FIGS. 2-9 above. Otherwise, the elements of thecell 22 h in FIG. 12 that are the same as the elements of thecell 22 in FIG. 3A are provided with the same numeral designations except that an “h” has been added to the numeral designations in FIG. 12. - It is not necessary that the
struts cell 22 in FIG. 3A, except that eachstrut 24 i, 30 i, 36 i and 42 i is now completely curved. Otherwise, the elements of the cell 22 i in FIG. 13 that are the same as the elements of thecell 22 in FIG. 3A are provided with the same numeral designations except that an “i” has been added to the numeral designations in FIG. 13. - The
cells 22 j in the stent pattern in FIG. 14 borrow from the principles illustrated in FIGS. 3A and 13. Each strut in thecells 22 j are made up of two strut pieces that have their respective ends connected at theapices 48 j, 50 j, 52 j and 54 j. In particular, thefirst strut 24 j has an accompanying inner strut piece 24 k whose ends are also connected to theapices 48 j and 52 j, the second strut 30 j has an accompanying inner strut piece 30 k whose ends are also connected to the apices 48 j and 54 j, the third strut 36 j has an accompanying inner strut piece 36 k whose ends are also connected to theapices 50 j and 52 j, and the fourth strut 42 j has an accompanying inner strut piece 42 k whose ends are also connected to the apices 50 j and 54 j. Eachstrut 24 j, 30 j, 36 j, 42 j and its accompanying inner strut piece 24 k, 30 k, 36 k, 42 k defines asmaller cell corresponding strut 24 j, 30 j, 36 j, 42 j. - Providing double struts to make up the desired
cells 22 j can provide certain benefits. First, the double-strut structure may increase the strength of the stent by providing radial and longitudinal resistance to compression and other changes in shape. Second, the resulting stent may have an increased expansion ratio. Third, the double-strut structure may reduce the tendency of the stent to recoil. Fourth, the resulting stent may have increased stent coverage and cells that have smaller sizes, thereby minimizing tissue in-growth. The double-strut embodiment of FIG. 14 can be especially useful in applications where the prosthesis requires increased support throughout the prosthesis while minimizing the potential for stent kink or breakage at certain regions along the stent. - FIG. 15A illustrates a stent20 m in which the
cells 22 m are essentially the same as the cell 22 i in FIG. 13, except that eachstrut strut inflection 64 m and one external point ofinflection 62 m. Otherwise, the elements of thecell 22 m in FIG. 15 that are the same as the elements of the cell 22 i in FIG. 13 are provided with the same numeral designations except that an “m” has been added to the numeral designations in FIG. 15. Similar to FIG. 2A, the pattern ofcells 22 m can define a second pattern of cells 22 y that have about the same configuration as thecells 22 m, but reversed about a horizontal axis defined by the apices 48 m and 50 m. Like thecells 22 m, these second cells 22 y are also arranged to form rows and columns of cells 22 y. Each of the second cells 22 y is defined by a separate strut from fourseparate cells 22 m. FIG. 15B illustrates the stent 20 m in the compressed state. One difference between thecell 22 m and theother cells 22 herein is that the apex 54 m in eachcell 22 m is inverted internally into thecell 22 m, as opposed to extending externally from thecell 22 m. - While the embodiments illustrated hereinabove illustrate stent patterns that are made up entirely of
cells 22 that have compensatingportions 60, it is also possible to intersperse cells that do not have any compensatingportions 60. These principles will be illustrated in FIGS. 16-18 using thecell pattern 22 m of FIG. 15. Referring first to FIG. 16, a stent 20 m is illustrated as having acentral portion 150 made up of a plurality of conventional zig-zag struts that do not have any compensating portions, and which form diamond-shapedcells 152. The two ends of the stent 20 m is made up of thecell pattern 22 m illustrated in FIG. 15. This configuration provides more rigidity in thecentral portion 150, and is better suited for use, for example, in the carotid arteries where more calcified lesions can be found at about thecentral portion 150, and where there is more potential for embolization in thecentral portion 150. This is because the diamond-shapedcells 152 are better suited to minimize embolization and prevent tissue in-growth. - FIG. 17 illustrates a
stent 20 n having afirst portion 154 made up of a plurality of conventional zig-zag struts that do not have any compensating portions, and which form diamond-shapedcells 152, and asecond portion 156 that is made up of thecell pattern 22 m illustrated in FIG. 15. Thefirst portion 154 can be used to support a body vessel at a location that requires more rigidity, and thesecond portion 156 can be used to support a body vessel at a location that requires more flexibility. This configuration is better suited for use, for example, in the iliac arteries where the origin of the iliac arteries might have more calcified lesions where thefirst portion 154 would be intended to support. - FIG. 18 illustrates a stent20
p having rows 158 ofcells 22 m separated by one or more rows of the diamond-shapedcells 152. Therows 158 can be individual rows ofcells 22 m, or a plurality of rows ofcells 22 m. This configuration is useful in distributing the radial strength of the stent 20 p while allowing for nonforeshortening and increased flexion at the desired locations (i.e., supported by thecells 22 m). This configuration is best suited for use, for example, with curved vessels such as external iliac arteries. - A number of materials can be used to fabricate the stent20 (including its
struts - The stent20 can be made from one of a number of methods, depending on the material of the stent 20 and the desired nature of deployment.
- In a non-limiting first preferred method, the stent20 is fabricated from a solid Nitinol tube with dimensions that are identical to the stent 20 when it is in the fully compressed state. The pattern of the stent 20 (i.e., its cells 22) is programmed into a computer-guided laser cutter which cuts out the segments between the struts and the connecting members (if any) in a manner which closely maintains the outside diameter and wall thickness of the stent 20.
- After the cutting step, the stent20 is progressively expanded until it reaches its fully expanded state. The expansion can be performed by an internal expansion fixture, although other expansion apparatus and methods can be used without departing from the spirit and scope of the present invention. The overall length of the stent 20 must be consistently maintained throughout the expansion of the stent 20 from its fully compressed to its fully expanded states.
- Once the stent20 has been expanded to its fully expanded state, it is heat-treated to “set” the shape memory of the Nitinol material so that it will fully return to its expanded dimensions at a temperature that is near body temperature. The stent 20 is then cleaned and electro-polished.
- The next step is to compress the stent20 again into a dimension which allows for delivery into a vessel, either through percutaneous delivery or through minimally invasive surgical procedures. Specifically, the stent 20 must be compressed into a smaller state so that it can be delivered by a delivery device to the desired location of the vessel. Any conventional delivery device could be used, such as but not limited to a tube, catheter, or sheath. This compression is accomplished by cooling the stent 20 to a low temperature, for example, zero degrees Celcius, and while maintaining this temperature, compressing the stent 20 to allow the stent 20 to be inserted inside the delivery device. Once inserted inside the delivery device, the stent 20 is held by the delivery device in the compressed state until it is released within the lumen of a vessel, at which time the stent will fully re-expand to its “set” dimensions as it equilibrates with body temperature.
- In a non-limiting second preferred method, a balloon-expandable stent20 can be fabricated by connecting a plurality of wires that have been bent or formed into the desired shapes for the
struts members 80. The connection can be accomplished by welding, tying, bonding, or any other conventional method. Alternatively, wire electro-discharge machining or a computer guided laser cutter can be used. The wires are capable of experiencing plastic deformation when the stent 20 is compressed, and when the stent 20 is expanded. Upon plastic deformation of the stent 20 to either the compressed or the expanded state, the stent 20 remains in this state until another force is applied to plastically deform the stent 20 again. - While certain methods of manufacture have been described above, it will be appreciated by those skilled in the art that other methods of manufacture can be utilized without departing from the spirit and scope of the present invention.
- The stent20 can be deployed by a number of delivery systems and delivery methods. These delivery systems and methods will vary depending on whether the stent 20 is expanded by self-expansion, radial expansion forces, or radio frequency. These delivery methods are well-known in the art, and shall not be described in greater detail herein.
- Thus, the present invention provides a stent having struts that include portions that compensate for the foreshortening effect. As a result, connecting members can be omitted from the stent designs according to the present invention, leading to at least the following benefits. First, cell sizes can be decreased so as to minimize “in-stent restenosis”, and to provide better support to the vessel. Second, the stent can be provided with a more uniform structure that distributes any angulation or flexion of the stent more evenly along the full length of the stent, so that the stent can experience a more gradual curvature at bends rather than experiencing undesirable kinking at such regions. This further minimizes breakage or other damage to the stent. Of course, connecting members can be optionally added to increase the flexibility of the stent at certain desired areas.
- While the description above refers to particular embodiments of the present invention, it will be understood that many modifications may be made without departing from the spirit thereof. The accompanying claims are intended to cover such modifications as would fall within the true scope and spirit of the present invention.
Claims (22)
1. A stent comprising:
a plurality of cells disposed about the circumference of the stent, with at least one cell having a plurality of struts that are connected together to form the cell, with at least one strut having a compensating portion that compensates for foreshortening of the struts during expansion of the stent.
2. The stent of , further including a connecting member for coupling two adjacent cells.
claim 1
3. The stent of , wherein the compensating portion has at least one area of inflection.
claim 1
4. The stent of , wherein the compensating portion has an internal area of inflection and an external area of inflection.
claim 1
5. The stent of , wherein each of the struts has a compensating portion.
claim 1
6. The stent of , wherein each of the plurality of cells has four struts that define a generally diamond-shaped configuration having four apices, with a compensating portion provided at one of the apices.
claim 1
7. The stent of , wherein a compensating portion is provided at two of the apices.
claim 6
8. The stent of , wherein a compensating portion is provided at all the apices.
claim 6
9. The stent of , wherein the compensating portion is C-shaped.
claim 6
10. The stent of , wherein the compensating portion is connects apices between two adjacent cells.
claim 6
11. The stent of , wherein the compensating portion is S-shaped.
claim 10
12. The stent of , wherein the compensating portion is C-shaped.
claim 10
13. The stent of , wherein each strut is completely curved.
claim 1
14. The stent of , wherein the plurality of cells is a first plurality of cells that defines a first plurality of rows and columns, and wherein the stent further includes a second plurality of cells that defines a second plurality of rows and columns.
claim 1
15. The stent of , wherein the configuration of the first plurality of cells is a substantial mirror image of the second plurality of cells.
claim 14
16. The stent of , wherein the plurality of cells is a first plurality of cells that is provided along a first length of the stent, and wherein the stent further includes a second plurality of cells that-is provided along a second length of the stent.
claim 1
17. The stent of , wherein the compensating portion is curved.
claim 1
18. The stent of , wherein each cell has a plurality of apices that are defined by the plurality of struts, and each of the plurality of struts includes a first strut and a second strut to define a double-strut configuration, with each of the first and second struts having a first end and a second end, wherein the first ends of the first and second struts are connected to a first apex, and the second ends of the first and second struts are connected to a second apex.
claim 1
19. The stent of , wherein the first and second struts of each of the plurality of struts defines a space therebetween.
claim 18
20. A stent comprising a plurality of cells disposed about the circumference of the stent, with at least one cell having a plurality of double-struts that are connected together to form the cell.
21. The stent of , wherein each cell has a plurality of apices that are defined by the plurality of double-struts, and with each of double-struts having a first end and a second end, wherein the first ends of the double-struts are connected to a first apex, and the second ends of the double-struts are connected to a second apex.
claim 20
22. The stent of , wherein each double-strut defines a space therebetween.
claim 21
Priority Applications (8)
Application Number | Priority Date | Filing Date | Title |
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US09/416,994 US20010047200A1 (en) | 1999-10-13 | 1999-10-13 | Non-foreshortening intraluminal prosthesis |
CA002386335A CA2386335C (en) | 1999-10-13 | 2000-10-12 | Non-foreshortening intraluminal prothesis |
AU11999/01A AU779189B2 (en) | 1999-10-13 | 2000-10-12 | Non-foreshortening intraluminal prosthesis |
JP2001529376A JP2003523792A (en) | 1999-10-13 | 2000-10-12 | Non-shortened endoluminal prosthesis |
EP00973496A EP1233723A4 (en) | 1999-10-13 | 2000-10-12 | Non-foreshortening intraluminal prosthesis |
PCT/US2000/028281 WO2001026583A1 (en) | 1999-10-13 | 2000-10-12 | Non-foreshortening intraluminal prosthesis |
US10/051,433 US6881222B2 (en) | 1999-10-13 | 2002-01-18 | Non-foreshortening intraluminal prosthesis |
US11/107,088 US8721705B2 (en) | 1999-10-13 | 2005-04-14 | Non-foreshortening intraluminal prosthesis |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
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US09/416,994 US20010047200A1 (en) | 1999-10-13 | 1999-10-13 | Non-foreshortening intraluminal prosthesis |
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US10/051,433 Division US6881222B2 (en) | 1999-10-13 | 2002-01-18 | Non-foreshortening intraluminal prosthesis |
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US09/416,994 Abandoned US20010047200A1 (en) | 1999-10-13 | 1999-10-13 | Non-foreshortening intraluminal prosthesis |
US10/051,433 Expired - Fee Related US6881222B2 (en) | 1999-10-13 | 2002-01-18 | Non-foreshortening intraluminal prosthesis |
US11/107,088 Expired - Fee Related US8721705B2 (en) | 1999-10-13 | 2005-04-14 | Non-foreshortening intraluminal prosthesis |
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Application Number | Title | Priority Date | Filing Date |
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US10/051,433 Expired - Fee Related US6881222B2 (en) | 1999-10-13 | 2002-01-18 | Non-foreshortening intraluminal prosthesis |
US11/107,088 Expired - Fee Related US8721705B2 (en) | 1999-10-13 | 2005-04-14 | Non-foreshortening intraluminal prosthesis |
Country Status (6)
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US (3) | US20010047200A1 (en) |
EP (1) | EP1233723A4 (en) |
JP (1) | JP2003523792A (en) |
AU (1) | AU779189B2 (en) |
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Cited By (50)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2003092549A2 (en) * | 2002-05-06 | 2003-11-13 | Abbott Laboratories | Endoprosthesis for controlled contraction and expansion |
US6679911B2 (en) * | 2001-03-01 | 2004-01-20 | Cordis Corporation | Flexible stent |
US6820676B2 (en) | 1999-11-19 | 2004-11-23 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal device exhibiting improved endothelialization and method of manufacture thereof |
US20050182477A1 (en) * | 2001-12-20 | 2005-08-18 | White Geoffrey H. | Intraluminal stent and graft |
US20060122691A1 (en) * | 1998-12-03 | 2006-06-08 | Jacob Richter | Hybrid stent |
US7122049B2 (en) | 2003-03-19 | 2006-10-17 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal stent having mid-strut interconnecting members |
US20090171426A1 (en) * | 2007-12-28 | 2009-07-02 | Cook Incorporated | Radially expandable stent |
US7625401B2 (en) | 2003-05-06 | 2009-12-01 | Abbott Laboratories | Endoprosthesis having foot extensions |
US7704274B2 (en) | 2002-09-26 | 2010-04-27 | Advanced Bio Prothestic Surfaces, Ltd. | Implantable graft and methods of making same |
US20110009875A1 (en) * | 2009-07-08 | 2011-01-13 | Concentric Medical, Inc. | Embolic obstruction retrieval devices and methods |
US20110009940A1 (en) * | 2009-07-08 | 2011-01-13 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US20110009941A1 (en) * | 2009-07-08 | 2011-01-13 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US20110009950A1 (en) * | 2009-07-08 | 2011-01-13 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US7985249B2 (en) | 2002-05-08 | 2011-07-26 | Abbott Laboratories Corporation | Endoprosthesis having foot extensions |
US20110184456A1 (en) * | 2009-07-08 | 2011-07-28 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US8048146B2 (en) | 2003-05-06 | 2011-11-01 | Abbott Laboratories | Endoprosthesis having foot extensions |
US8092514B1 (en) * | 1998-11-16 | 2012-01-10 | Boston Scientific Scimed, Inc. | Stretchable anti-buckling coiled-sheet stent |
US20130131788A1 (en) * | 2008-09-29 | 2013-05-23 | Cardiaq Valve Technologies, Inc. | Body cavity prosthesis |
US8529596B2 (en) | 2009-07-08 | 2013-09-10 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US8641754B2 (en) * | 2000-11-07 | 2014-02-04 | Advanced Bio Prosthetic Surfaces, Ltd. a wholly owned subsidiary of Palmaz Scientific, Inc. | Endoluminal stent, self-supporting endoluminal graft and methods of making same |
US20140172086A1 (en) * | 2009-04-15 | 2014-06-19 | Cardiaq Valve Technologies, Inc. | Vascular implant and delivery system |
US8911455B2 (en) | 2008-10-01 | 2014-12-16 | Cardiaq Valve Technologies, Inc. | Delivery system for vascular implant |
US20140371839A1 (en) * | 2002-07-19 | 2014-12-18 | Covidien Lp | Medical implant having a curlable matrix structure and method of use |
US8974514B2 (en) | 2007-03-13 | 2015-03-10 | Abbott Cardiovascular Systems Inc. | Intravascular stent with integrated link and ring strut |
US9023100B2 (en) | 2009-09-29 | 2015-05-05 | Cardiaq Valve Technologies, Inc. | Replacement heart valves, delivery devices and methods |
US9072537B2 (en) | 2009-07-08 | 2015-07-07 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
USD755384S1 (en) | 2014-03-05 | 2016-05-03 | Edwards Lifesciences Cardiaq Llc | Stent |
US9433514B2 (en) | 2005-11-10 | 2016-09-06 | Edwards Lifesciences Cardiaq Llc | Method of securing a prosthesis |
US9480560B2 (en) | 2009-09-29 | 2016-11-01 | Edwards Lifesciences Cardiaq Llc | Method of securing an intralumenal frame assembly |
US9554897B2 (en) | 2011-04-28 | 2017-01-31 | Neovasc Tiara Inc. | Methods and apparatus for engaging a valve prosthesis with tissue |
US9572665B2 (en) | 2013-04-04 | 2017-02-21 | Neovasc Tiara Inc. | Methods and apparatus for delivering a prosthetic valve to a beating heart |
US9681951B2 (en) | 2013-03-14 | 2017-06-20 | Edwards Lifesciences Cardiaq Llc | Prosthesis with outer skirt and anchors |
US9713529B2 (en) | 2011-04-28 | 2017-07-25 | Neovasc Tiara Inc. | Sequentially deployed transcatheter mitral valve prosthesis |
US9724083B2 (en) | 2013-07-26 | 2017-08-08 | Edwards Lifesciences Cardiaq Llc | Systems and methods for sealing openings in an anatomical wall |
US9730791B2 (en) | 2013-03-14 | 2017-08-15 | Edwards Lifesciences Cardiaq Llc | Prosthesis for atraumatically grasping intralumenal tissue and methods of delivery |
US9770329B2 (en) | 2010-05-05 | 2017-09-26 | Neovasc Tiara Inc. | Transcatheter mitral valve prosthesis |
US9956320B2 (en) | 2003-06-27 | 2018-05-01 | Zuli Holdings Ltd. | Amorphous metal alloy medical devices |
US10016275B2 (en) | 2012-05-30 | 2018-07-10 | Neovasc Tiara Inc. | Methods and apparatus for loading a prosthesis onto a delivery system |
US10213298B2 (en) | 2004-03-11 | 2019-02-26 | Percutaneous Cardiovascular Solutions Pty Ltd | Percutaneous heart valve prosthesis |
US10271977B2 (en) | 2017-09-08 | 2019-04-30 | Vesper Medical, Inc. | Hybrid stent |
US10350062B2 (en) | 2016-07-21 | 2019-07-16 | Edwards Lifesciences Corporation | Replacement heart valve prosthesis |
US10363152B2 (en) | 2003-06-27 | 2019-07-30 | Medinol Ltd. | Helical hybrid stent |
US10500078B2 (en) | 2018-03-09 | 2019-12-10 | Vesper Medical, Inc. | Implantable stent |
US10583002B2 (en) | 2013-03-11 | 2020-03-10 | Neovasc Tiara Inc. | Prosthetic valve with anti-pivoting mechanism |
US10702405B2 (en) | 2016-03-31 | 2020-07-07 | Vesper Medical, Inc. | Intravascular implants |
US10849769B2 (en) | 2017-08-23 | 2020-12-01 | Vesper Medical, Inc. | Non-foreshortening stent |
US11357650B2 (en) | 2019-02-28 | 2022-06-14 | Vesper Medical, Inc. | Hybrid stent |
US11364134B2 (en) | 2018-02-15 | 2022-06-21 | Vesper Medical, Inc. | Tapering stent |
US11628076B2 (en) | 2017-09-08 | 2023-04-18 | Vesper Medical, Inc. | Hybrid stent |
US11684474B2 (en) | 2018-01-25 | 2023-06-27 | Edwards Lifesciences Corporation | Delivery system for aided replacement valve recapture and repositioning post-deployment |
Families Citing this family (54)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20060173531A1 (en) * | 1996-09-19 | 2006-08-03 | Jacob Richter | Stent with variable features to optimize support and method of making such stent |
US5807404A (en) * | 1996-09-19 | 1998-09-15 | Medinol Ltd. | Stent with variable features to optimize support and method of making such stent |
US5827321A (en) * | 1997-02-07 | 1998-10-27 | Cornerstone Devices, Inc. | Non-Foreshortening intraluminal prosthesis |
US7815763B2 (en) * | 2001-09-28 | 2010-10-19 | Abbott Laboratories Vascular Enterprises Limited | Porous membranes for medical implants and methods of manufacture |
US7887578B2 (en) | 1998-09-05 | 2011-02-15 | Abbott Laboratories Vascular Enterprises Limited | Stent having an expandable web structure |
US20020019660A1 (en) * | 1998-09-05 | 2002-02-14 | Marc Gianotti | Methods and apparatus for a curved stent |
US6755856B2 (en) * | 1998-09-05 | 2004-06-29 | Abbott Laboratories Vascular Enterprises Limited | Methods and apparatus for stenting comprising enhanced embolic protection, coupled with improved protection against restenosis and thrombus formation |
US6682554B2 (en) * | 1998-09-05 | 2004-01-27 | Jomed Gmbh | Methods and apparatus for a stent having an expandable web structure |
US20010047200A1 (en) * | 1999-10-13 | 2001-11-29 | Raymond Sun | Non-foreshortening intraluminal prosthesis |
US8496699B2 (en) * | 2000-03-01 | 2013-07-30 | Medinol Ltd. | Longitudinally flexible stent |
US7758627B2 (en) * | 2000-03-01 | 2010-07-20 | Medinol, Ltd. | Longitudinally flexible stent |
US8920487B1 (en) | 2000-03-01 | 2014-12-30 | Medinol Ltd. | Longitudinally flexible stent |
US7141062B1 (en) * | 2000-03-01 | 2006-11-28 | Medinol, Ltd. | Longitudinally flexible stent |
US8202312B2 (en) * | 2000-03-01 | 2012-06-19 | Medinol Ltd. | Longitudinally flexible stent |
US9522217B2 (en) | 2000-03-15 | 2016-12-20 | Orbusneich Medical, Inc. | Medical device with coating for capturing genetically-altered cells and methods for using same |
US8460367B2 (en) | 2000-03-15 | 2013-06-11 | Orbusneich Medical, Inc. | Progenitor endothelial cell capturing with a drug eluting implantable medical device |
US8088060B2 (en) | 2000-03-15 | 2012-01-03 | Orbusneich Medical, Inc. | Progenitor endothelial cell capturing with a drug eluting implantable medical device |
US8070792B2 (en) | 2000-09-22 | 2011-12-06 | Boston Scientific Scimed, Inc. | Stent |
EP1516600B1 (en) * | 2001-09-18 | 2007-03-14 | Abbott Laboratories Vascular Enterprises Limited | Stent |
US20030074051A1 (en) * | 2001-10-16 | 2003-04-17 | Kirsten Freislinger Luehrs | Flexible stent |
US20030176914A1 (en) * | 2003-01-21 | 2003-09-18 | Rabkin Dmitry J. | Multi-segment modular stent and methods for manufacturing stents |
US20040054398A1 (en) * | 2002-09-13 | 2004-03-18 | Cully Edward H. | Stent device with multiple helix construction |
US7637942B2 (en) * | 2002-11-05 | 2009-12-29 | Merit Medical Systems, Inc. | Coated stent with geometry determinated functionality and method of making the same |
US7959671B2 (en) | 2002-11-05 | 2011-06-14 | Merit Medical Systems, Inc. | Differential covering and coating methods |
US7875068B2 (en) | 2002-11-05 | 2011-01-25 | Merit Medical Systems, Inc. | Removable biliary stent |
US7625398B2 (en) * | 2003-05-06 | 2009-12-01 | Abbott Laboratories | Endoprosthesis having foot extensions |
DE10342759A1 (en) * | 2003-09-16 | 2005-04-14 | Campus Gmbh & Co. Kg | Stent with improved durability |
US7887579B2 (en) * | 2004-09-29 | 2011-02-15 | Merit Medical Systems, Inc. | Active stent |
US20060190072A1 (en) * | 2005-01-28 | 2006-08-24 | Das Gladwin S | Flexible cells for axially interconnecting stent components |
US7731654B2 (en) * | 2005-05-13 | 2010-06-08 | Merit Medical Systems, Inc. | Delivery device with viewing window and associated method |
GB0609841D0 (en) * | 2006-05-17 | 2006-06-28 | Angiomed Ag | Bend-capable tubular prosthesis |
EP2043570B1 (en) * | 2006-07-10 | 2018-10-31 | First Quality Hygienic, Inc. | Resilient device |
US10004584B2 (en) | 2006-07-10 | 2018-06-26 | First Quality Hygienic, Inc. | Resilient intravaginal device |
US10219884B2 (en) | 2006-07-10 | 2019-03-05 | First Quality Hygienic, Inc. | Resilient device |
US8613698B2 (en) * | 2006-07-10 | 2013-12-24 | Mcneil-Ppc, Inc. | Resilient device |
US8177706B2 (en) * | 2006-07-10 | 2012-05-15 | Mcneil-Ppc, Inc. | Method of treating urinary incontinence |
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 |
US7850726B2 (en) | 2007-12-20 | 2010-12-14 | Abbott Laboratories Vascular Enterprises Limited | Endoprosthesis having struts linked by foot extensions |
US8920488B2 (en) * | 2007-12-20 | 2014-12-30 | Abbott Laboratories Vascular Enterprises Limited | Endoprosthesis having a stable architecture |
US8337544B2 (en) * | 2007-12-20 | 2012-12-25 | Abbott Laboratories Vascular Enterprises Limited | Endoprosthesis having flexible connectors |
JP4852631B2 (en) * | 2009-06-28 | 2012-01-11 | 株式会社沖データ | Communication device and connection control method thereof |
US20110152604A1 (en) * | 2009-12-23 | 2011-06-23 | Hull Jr Raymond J | Intravaginal incontinence device |
JP5847160B2 (en) * | 2011-03-25 | 2016-01-20 | テルモ株式会社 | Stent and stent delivery system |
BR112014028242B1 (en) | 2012-05-14 | 2021-04-13 | C.R. Bard, Inc | INTRALUMINAL PROSTHESIS |
EP3375411A1 (en) * | 2012-12-31 | 2018-09-19 | Edwards Lifesciences Corporation | Surgical heart valves adapted for post-implant expansion |
USD723165S1 (en) | 2013-03-12 | 2015-02-24 | C. R. Bard, Inc. | Stent |
US10271975B2 (en) | 2013-03-15 | 2019-04-30 | Atrium Medical Corporation | Stent device having reduced foreshortening and recoil and method of making same |
DE102014016588A1 (en) * | 2014-11-11 | 2016-05-12 | medicut Stent Technology GmbH | stent graft |
CN107708620B (en) * | 2015-06-11 | 2020-09-11 | 北京阿迈特医疗器械有限公司 | Support with closed-loop structure, preparation method and application thereof |
GB201611469D0 (en) | 2016-06-30 | 2016-08-17 | Lumiradx Tech Ltd | Improvements in or relating to nucleic acid amplification processes |
RU2753447C2 (en) * | 2016-10-04 | 2021-08-16 | Ясухиро СЁБАЯСИ | Flexible stent |
GB2569965A (en) | 2018-01-04 | 2019-07-10 | Lumiradx Uk Ltd | Improvements in or relating to amplification of nucleic acids |
EP4257095B1 (en) * | 2022-04-04 | 2024-04-03 | Sanita Biosciences BV | Flexible stent and method for manufacturing the same |
Family Cites Families (35)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5356423A (en) | 1991-01-04 | 1994-10-18 | American Medical Systems, Inc. | Resectable self-expanding stent |
CA2079417C (en) | 1991-10-28 | 2003-01-07 | Lilip Lau | Expandable stents and method of making same |
US5540712A (en) | 1992-05-01 | 1996-07-30 | Nitinol Medical Technologies, Inc. | Stent and method and apparatus for forming and delivering the same |
US5643312A (en) | 1994-02-25 | 1997-07-01 | Fischell Robert | Stent having a multiplicity of closed circular structures |
US5449373A (en) * | 1994-03-17 | 1995-09-12 | Medinol Ltd. | Articulated stent |
US5733303A (en) | 1994-03-17 | 1998-03-31 | Medinol Ltd. | Flexible expandable stent |
US6461381B2 (en) | 1994-03-17 | 2002-10-08 | Medinol, Ltd. | Flexible expandable stent |
DE4418336A1 (en) | 1994-05-26 | 1995-11-30 | Angiomed Ag | Stent for widening and holding open receptacles |
DE69637527D1 (en) | 1995-03-01 | 2008-06-26 | Boston Scient Scimed Inc | Longitudinally flexible and expandable stent |
US5980553A (en) * | 1996-12-20 | 1999-11-09 | Cordis Corporation | Axially flexible stent |
US5695516A (en) * | 1996-02-21 | 1997-12-09 | Iso Stent, Inc. | Longitudinally elongating balloon expandable stent |
US5922021A (en) * | 1996-04-26 | 1999-07-13 | Jang; G. David | Intravascular stent |
US5776183A (en) * | 1996-08-23 | 1998-07-07 | Kanesaka; Nozomu | Expandable stent |
US5807404A (en) * | 1996-09-19 | 1998-09-15 | Medinol Ltd. | Stent with variable features to optimize support and method of making such stent |
US5868781A (en) | 1996-10-22 | 1999-02-09 | Scimed Life Systems, Inc. | Locking stent |
US6206911B1 (en) * | 1996-12-19 | 2001-03-27 | Simcha Milo | Stent combination |
US5827321A (en) * | 1997-02-07 | 1998-10-27 | Cornerstone Devices, Inc. | Non-Foreshortening intraluminal prosthesis |
US5810872A (en) | 1997-03-14 | 1998-09-22 | Kanesaka; Nozomu | Flexible stent |
US5836966A (en) | 1997-05-22 | 1998-11-17 | Scimed Life Systems, Inc. | Variable expansion force stent |
US5913895A (en) * | 1997-06-02 | 1999-06-22 | Isostent, Inc. | Intravascular stent with enhanced rigidity strut members |
US5855600A (en) | 1997-08-01 | 1999-01-05 | Inflow Dynamics Inc. | Flexible implantable stent with composite design |
US5824059A (en) | 1997-08-05 | 1998-10-20 | Wijay; Bandula | Flexible stent |
US6059822A (en) * | 1997-08-22 | 2000-05-09 | Uni-Cath Inc. | Stent with different mesh patterns |
US6042606A (en) | 1997-09-29 | 2000-03-28 | Cook Incorporated | Radially expandable non-axially contracting surgical stent |
FR2768919B1 (en) * | 1997-10-01 | 1999-11-19 | Braun Celsa Sa | EXPANDABLE SUPPORT FOR ANATOMICAL DUCT |
US6013091A (en) * | 1997-10-09 | 2000-01-11 | Scimed Life Systems, Inc. | Stent configurations |
US5938697A (en) | 1998-03-04 | 1999-08-17 | Scimed Life Systems, Inc. | Stent having variable properties |
DE69931472T2 (en) * | 1998-03-04 | 2006-09-28 | Boston Scientific Ltd., St. Michael | STENT WITH IMPROVED CELL CONFIGURATION |
US6132460A (en) * | 1998-03-27 | 2000-10-17 | Intratherapeutics, Inc. | Stent |
US6132461A (en) * | 1998-03-27 | 2000-10-17 | Intratherapeutics, Inc. | Stent with dual support structure |
FR2777771B1 (en) * | 1998-04-27 | 2000-08-25 | Microval | TUBULAR AND FLEXIBLE VASCULAR ENDOPROSTHESIS |
US6730116B1 (en) * | 1999-04-16 | 2004-05-04 | Medtronic, Inc. | Medical device for intraluminal endovascular stenting |
US6245101B1 (en) | 1999-05-03 | 2001-06-12 | William J. Drasler | Intravascular hinge stent |
US20010047200A1 (en) * | 1999-10-13 | 2001-11-29 | Raymond Sun | Non-foreshortening intraluminal prosthesis |
US6398806B1 (en) | 2000-12-26 | 2002-06-04 | Scimed Life Systems, Inc. | Monolayer modification to gold coated stents to reduce adsorption of protein |
-
1999
- 1999-10-13 US US09/416,994 patent/US20010047200A1/en not_active Abandoned
-
2000
- 2000-10-12 WO PCT/US2000/028281 patent/WO2001026583A1/en active IP Right Grant
- 2000-10-12 AU AU11999/01A patent/AU779189B2/en not_active Ceased
- 2000-10-12 JP JP2001529376A patent/JP2003523792A/en not_active Withdrawn
- 2000-10-12 CA CA002386335A patent/CA2386335C/en not_active Expired - Fee Related
- 2000-10-12 EP EP00973496A patent/EP1233723A4/en not_active Ceased
-
2002
- 2002-01-18 US US10/051,433 patent/US6881222B2/en not_active Expired - Fee Related
-
2005
- 2005-04-14 US US11/107,088 patent/US8721705B2/en not_active Expired - Fee Related
Cited By (122)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8092514B1 (en) * | 1998-11-16 | 2012-01-10 | Boston Scientific Scimed, Inc. | Stretchable anti-buckling coiled-sheet stent |
US20060122691A1 (en) * | 1998-12-03 | 2006-06-08 | Jacob Richter | Hybrid stent |
US6820676B2 (en) | 1999-11-19 | 2004-11-23 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal device exhibiting improved endothelialization and method of manufacture thereof |
US9284637B2 (en) | 1999-11-19 | 2016-03-15 | Advanced Bio Prosthetic Surfaces, Ltd., A Wholly Owned Subsidiary Of Palmaz Scientific, Inc. | Implantable graft and methods of making same |
US8641754B2 (en) * | 2000-11-07 | 2014-02-04 | Advanced Bio Prosthetic Surfaces, Ltd. a wholly owned subsidiary of Palmaz Scientific, Inc. | Endoluminal stent, self-supporting endoluminal graft and methods of making same |
US6679911B2 (en) * | 2001-03-01 | 2004-01-20 | Cordis Corporation | Flexible stent |
US20050182477A1 (en) * | 2001-12-20 | 2005-08-18 | White Geoffrey H. | Intraluminal stent and graft |
US20040093072A1 (en) * | 2002-05-06 | 2004-05-13 | Jeff Pappas | Endoprosthesis for controlled contraction and expansion |
WO2003092549A2 (en) * | 2002-05-06 | 2003-11-13 | Abbott Laboratories | Endoprosthesis for controlled contraction and expansion |
US7637935B2 (en) | 2002-05-06 | 2009-12-29 | Abbott Laboratories | Endoprosthesis for controlled contraction and expansion |
US20100063581A1 (en) * | 2002-05-06 | 2010-03-11 | Jeff Pappas | Endoprosthesis For Controlled Contraction And Expansion |
US8075610B2 (en) | 2002-05-06 | 2011-12-13 | Abbott Laboratories | Endoprosthesis for controlled contraction and expansion |
WO2003092549A3 (en) * | 2002-05-06 | 2004-04-08 | Abbott Lab | Endoprosthesis for controlled contraction and expansion |
US7985249B2 (en) | 2002-05-08 | 2011-07-26 | Abbott Laboratories Corporation | Endoprosthesis having foot extensions |
US20140371839A1 (en) * | 2002-07-19 | 2014-12-18 | Covidien Lp | Medical implant having a curlable matrix structure and method of use |
US10342683B2 (en) * | 2002-07-19 | 2019-07-09 | Ussc Medical Gmbh | Medical implant having a curlable matrix structure and method of use |
US11426293B2 (en) | 2002-07-19 | 2022-08-30 | Ussc Medical Gmbh | Medical implant |
US7704274B2 (en) | 2002-09-26 | 2010-04-27 | Advanced Bio Prothestic Surfaces, Ltd. | Implantable graft and methods of making same |
US10465274B2 (en) | 2002-09-26 | 2019-11-05 | Vactronix Scientific, Llc | Implantable graft and methods of making same |
US7980289B2 (en) | 2003-03-19 | 2011-07-19 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal stent having mid-strut interconnecting members |
US7122049B2 (en) | 2003-03-19 | 2006-10-17 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal stent having mid-strut interconnecting members |
US8048146B2 (en) | 2003-05-06 | 2011-11-01 | Abbott Laboratories | Endoprosthesis having foot extensions |
US7625401B2 (en) | 2003-05-06 | 2009-12-01 | Abbott Laboratories | Endoprosthesis having foot extensions |
US8109991B2 (en) | 2003-05-06 | 2012-02-07 | Abbot Laboratories | Endoprosthesis having foot extensions |
US8915954B2 (en) | 2003-05-06 | 2014-12-23 | Abbott Laboratories | Endoprosthesis having foot extensions |
US10363152B2 (en) | 2003-06-27 | 2019-07-30 | Medinol Ltd. | Helical hybrid stent |
US9956320B2 (en) | 2003-06-27 | 2018-05-01 | Zuli Holdings Ltd. | Amorphous metal alloy medical devices |
US11213390B2 (en) | 2004-03-11 | 2022-01-04 | Percutaneous Cardiovascular Solutions Pty Ltd | Method of implanting a heart valve prosthesis |
US10993806B2 (en) | 2004-03-11 | 2021-05-04 | Percutaneous Cardiovascular Solutions Pty Ltd | Percutaneous heart valve prosthesis |
US11744705B2 (en) | 2004-03-11 | 2023-09-05 | Percutaneous Cardiovascular Solutions Pty Ltd | Method of implanting a heart valve prosthesis |
US11622856B2 (en) | 2004-03-11 | 2023-04-11 | Percutaneous Cardiovascular Solutions Pty Ltd | Percutaneous heart valve prosthesis |
US10213298B2 (en) | 2004-03-11 | 2019-02-26 | Percutaneous Cardiovascular Solutions Pty Ltd | Percutaneous heart valve prosthesis |
US9974669B2 (en) | 2005-11-10 | 2018-05-22 | Edwards Lifesciences Cardiaq Llc | Percutaneous heart valve |
US9486336B2 (en) | 2005-11-10 | 2016-11-08 | Edwards Lifesciences Cardiaq Llc | Prosthesis having a plurality of distal and proximal prongs |
US9433514B2 (en) | 2005-11-10 | 2016-09-06 | Edwards Lifesciences Cardiaq Llc | Method of securing a prosthesis |
US10456277B2 (en) | 2005-11-10 | 2019-10-29 | Edwards Lifesciences Cardiaq Llc | Percutaneous heart valve |
US8974514B2 (en) | 2007-03-13 | 2015-03-10 | Abbott Cardiovascular Systems Inc. | Intravascular stent with integrated link and ring strut |
US20090171426A1 (en) * | 2007-12-28 | 2009-07-02 | Cook Incorporated | Radially expandable stent |
US8470021B2 (en) | 2007-12-28 | 2013-06-25 | Cook Medical Technologies Llc | Radially expandable stent |
US11819404B2 (en) | 2008-09-29 | 2023-11-21 | Edwards Lifesciences Cardiaq Llc | Heart valve |
US20130184813A1 (en) * | 2008-09-29 | 2013-07-18 | Cardiaq Valve Technologies, Inc. | Body cavity prosthesis |
US8894702B2 (en) * | 2008-09-29 | 2014-11-25 | Cardiaq Valve Technologies, Inc. | Replacement heart valve and method |
US10149756B2 (en) | 2008-09-29 | 2018-12-11 | Edwards Lifesciences Cardiaq Llc | Heart valve |
US10646334B2 (en) | 2008-09-29 | 2020-05-12 | Edwards Lifesciences Cardiaq Llc | Heart valve |
US20130131793A1 (en) * | 2008-09-29 | 2013-05-23 | Cardiaq Valve Technologies, Inc. | Replacement heart valve and method |
US11589983B2 (en) | 2008-09-29 | 2023-02-28 | Edwards Lifesciences Cardiaq Llc | Heart valve |
US20130131788A1 (en) * | 2008-09-29 | 2013-05-23 | Cardiaq Valve Technologies, Inc. | Body cavity prosthesis |
US9456896B2 (en) * | 2008-09-29 | 2016-10-04 | Edwards Lifesciences Cardiaq Llc | Body cavity prosthesis |
US9339377B2 (en) * | 2008-09-29 | 2016-05-17 | Edwards Lifesciences Cardiaq Llc | Body cavity prosthesis |
US8911455B2 (en) | 2008-10-01 | 2014-12-16 | Cardiaq Valve Technologies, Inc. | Delivery system for vascular implant |
US9597183B2 (en) | 2008-10-01 | 2017-03-21 | Edwards Lifesciences Cardiaq Llc | Delivery system for vascular implant |
US9585747B2 (en) * | 2009-04-15 | 2017-03-07 | Edwards Lifesciences Cardiaq Llc | Vascular implant |
US20140309731A1 (en) * | 2009-04-15 | 2014-10-16 | Cardiaq Valve Technologies, Inc. | Vascular implant |
US9339380B2 (en) * | 2009-04-15 | 2016-05-17 | Edwards Lifesciences Cardiaq Llc | Vascular implant |
US9339379B2 (en) | 2009-04-15 | 2016-05-17 | Edwards Lifesciences Cardiaq Llc | Vascular implant and delivery system |
US11376119B2 (en) * | 2009-04-15 | 2022-07-05 | Edwards Lifesciences Cardiaq Llc | Vascular implant and delivery system |
US9333073B2 (en) | 2009-04-15 | 2016-05-10 | Edwards Lifesciences Cardiaq Llc | Vascular implant and delivery method |
US9339378B2 (en) | 2009-04-15 | 2016-05-17 | Edwards Lifesciences Cardiaq Llc | Vascular implant and delivery system |
US20140172086A1 (en) * | 2009-04-15 | 2014-06-19 | Cardiaq Valve Technologies, Inc. | Vascular implant and delivery system |
US9333074B2 (en) | 2009-04-15 | 2016-05-10 | Edwards Lifesciences Cardiaq Llc | Vascular implant and delivery system |
US8795356B2 (en) | 2009-04-15 | 2014-08-05 | Cardiaq Valve Technologies, Inc. | Vascular implant |
US20110009950A1 (en) * | 2009-07-08 | 2011-01-13 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US8357178B2 (en) | 2009-07-08 | 2013-01-22 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US20110009941A1 (en) * | 2009-07-08 | 2011-01-13 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US20110184456A1 (en) * | 2009-07-08 | 2011-07-28 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US8795345B2 (en) | 2009-07-08 | 2014-08-05 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US8529596B2 (en) | 2009-07-08 | 2013-09-10 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US8795317B2 (en) | 2009-07-08 | 2014-08-05 | Concentric Medical, Inc. | Embolic obstruction retrieval devices and methods |
US9072537B2 (en) | 2009-07-08 | 2015-07-07 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US9044263B2 (en) | 2009-07-08 | 2015-06-02 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US8357179B2 (en) | 2009-07-08 | 2013-01-22 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US20110009875A1 (en) * | 2009-07-08 | 2011-01-13 | Concentric Medical, Inc. | Embolic obstruction retrieval devices and methods |
US20110009940A1 (en) * | 2009-07-08 | 2011-01-13 | Concentric Medical, Inc. | Vascular and bodily duct treatment devices and methods |
US9949827B2 (en) | 2009-09-29 | 2018-04-24 | Edwards Lifesciences Cardiaq Llc | Replacement heart valves, delivery devices and methods |
US9730790B2 (en) | 2009-09-29 | 2017-08-15 | Edwards Lifesciences Cardiaq Llc | Replacement valve and method |
US10166097B2 (en) | 2009-09-29 | 2019-01-01 | Edwards Lifesciences Cardiaq Llc | Replacement heart valve and method |
US9023100B2 (en) | 2009-09-29 | 2015-05-05 | Cardiaq Valve Technologies, Inc. | Replacement heart valves, delivery devices and methods |
US9480560B2 (en) | 2009-09-29 | 2016-11-01 | Edwards Lifesciences Cardiaq Llc | Method of securing an intralumenal frame assembly |
US9770329B2 (en) | 2010-05-05 | 2017-09-26 | Neovasc Tiara Inc. | Transcatheter mitral valve prosthesis |
US11432924B2 (en) | 2010-05-05 | 2022-09-06 | Neovasc Tiara Inc. | Transcatheter mitral valve prosthesis |
US10449042B2 (en) | 2010-05-05 | 2019-10-22 | Neovasc Tiara Inc. | Transcatheter mitral valve prosthesis |
US11419720B2 (en) | 2010-05-05 | 2022-08-23 | Neovasc Tiara Inc. | Transcatheter mitral valve prosthesis |
US10881510B2 (en) | 2010-09-23 | 2021-01-05 | Edwards Lifesciences Cardiaq Llc | Replacement heart valves, delivery devices and methods |
US10610362B2 (en) | 2010-09-23 | 2020-04-07 | Edwards Lifesciences Cardiaq Llc | Replacement heart valves, delivery devices and methods |
US10779938B2 (en) | 2011-02-23 | 2020-09-22 | Edwards Lifesciences Cardiaq Llc | Replacement heart valve and method |
US11903825B2 (en) | 2011-02-23 | 2024-02-20 | Edwards Lifesciences Cardiaq Llc | Replacement heart valve and method |
US9713529B2 (en) | 2011-04-28 | 2017-07-25 | Neovasc Tiara Inc. | Sequentially deployed transcatheter mitral valve prosthesis |
US9554897B2 (en) | 2011-04-28 | 2017-01-31 | Neovasc Tiara Inc. | Methods and apparatus for engaging a valve prosthesis with tissue |
US10537422B2 (en) | 2011-11-23 | 2020-01-21 | Neovasc Tiara Inc. | Sequentially deployed transcatheter mitral valve prosthesis |
US11413139B2 (en) | 2011-11-23 | 2022-08-16 | Neovasc Tiara Inc. | Sequentially deployed transcatheter mitral valve prosthesis |
US10363133B2 (en) | 2012-02-14 | 2019-07-30 | Neovac Tiara Inc. | Methods and apparatus for engaging a valve prosthesis with tissue |
US11497602B2 (en) | 2012-02-14 | 2022-11-15 | Neovasc Tiara Inc. | Methods and apparatus for engaging a valve prosthesis with tissue |
US11389294B2 (en) | 2012-05-30 | 2022-07-19 | Neovasc Tiara Inc. | Methods and apparatus for loading a prosthesis onto a delivery system |
US10314705B2 (en) | 2012-05-30 | 2019-06-11 | Neovasc Tiara Inc. | Methods and apparatus for loading a prosthesis onto a delivery system |
US10016275B2 (en) | 2012-05-30 | 2018-07-10 | Neovasc Tiara Inc. | Methods and apparatus for loading a prosthesis onto a delivery system |
US11617650B2 (en) | 2012-05-30 | 2023-04-04 | Neovasc Tiara Inc. | Methods and apparatus for loading a prosthesis onto a delivery system |
US10940001B2 (en) | 2012-05-30 | 2021-03-09 | Neovasc Tiara Inc. | Methods and apparatus for loading a prosthesis onto a delivery system |
US10583002B2 (en) | 2013-03-11 | 2020-03-10 | Neovasc Tiara Inc. | Prosthetic valve with anti-pivoting mechanism |
US9681951B2 (en) | 2013-03-14 | 2017-06-20 | Edwards Lifesciences Cardiaq Llc | Prosthesis with outer skirt and anchors |
US9730791B2 (en) | 2013-03-14 | 2017-08-15 | Edwards Lifesciences Cardiaq Llc | Prosthesis for atraumatically grasping intralumenal tissue and methods of delivery |
US11389291B2 (en) | 2013-04-04 | 2022-07-19 | Neovase Tiara Inc. | Methods and apparatus for delivering a prosthetic valve to a beating heart |
US10383728B2 (en) | 2013-04-04 | 2019-08-20 | Neovasc Tiara Inc. | Methods and apparatus for delivering a prosthetic valve to a beating heart |
US9572665B2 (en) | 2013-04-04 | 2017-02-21 | Neovasc Tiara Inc. | Methods and apparatus for delivering a prosthetic valve to a beating heart |
US9724083B2 (en) | 2013-07-26 | 2017-08-08 | Edwards Lifesciences Cardiaq Llc | Systems and methods for sealing openings in an anatomical wall |
USD755384S1 (en) | 2014-03-05 | 2016-05-03 | Edwards Lifesciences Cardiaq Llc | Stent |
US11628075B2 (en) | 2016-03-31 | 2023-04-18 | Vesper Medical, Inc. | Intravascular implants |
US10702405B2 (en) | 2016-03-31 | 2020-07-07 | Vesper Medical, Inc. | Intravascular implants |
US10758381B2 (en) | 2016-03-31 | 2020-09-01 | Vesper Medical, Inc. | Intravascular implants |
US11484422B2 (en) | 2016-03-31 | 2022-11-01 | Vesper Medical, Inc. | Intravascular implants |
US10350062B2 (en) | 2016-07-21 | 2019-07-16 | Edwards Lifesciences Corporation | Replacement heart valve prosthesis |
US11224507B2 (en) | 2016-07-21 | 2022-01-18 | Edwards Lifesciences Corporation | Replacement heart valve prosthesis |
US10849769B2 (en) | 2017-08-23 | 2020-12-01 | Vesper Medical, Inc. | Non-foreshortening stent |
US11376142B2 (en) | 2017-09-08 | 2022-07-05 | Vesper Medical, Inc. | Hybrid stent |
US10271977B2 (en) | 2017-09-08 | 2019-04-30 | Vesper Medical, Inc. | Hybrid stent |
US10512556B2 (en) | 2017-09-08 | 2019-12-24 | Vesper Medical, Inc. | Hybrid stent |
US11628076B2 (en) | 2017-09-08 | 2023-04-18 | Vesper Medical, Inc. | Hybrid stent |
US10588764B2 (en) | 2017-09-08 | 2020-03-17 | Vesper Medical, Inc. | Hybrid stent |
US11684474B2 (en) | 2018-01-25 | 2023-06-27 | Edwards Lifesciences Corporation | Delivery system for aided replacement valve recapture and repositioning post-deployment |
US11364134B2 (en) | 2018-02-15 | 2022-06-21 | Vesper Medical, Inc. | Tapering stent |
US10500078B2 (en) | 2018-03-09 | 2019-12-10 | Vesper Medical, Inc. | Implantable stent |
US11344439B2 (en) | 2018-03-09 | 2022-05-31 | Vesper Medical, Inc. | Implantable stent |
US11357650B2 (en) | 2019-02-28 | 2022-06-14 | Vesper Medical, Inc. | Hybrid stent |
Also Published As
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US6881222B2 (en) | 2005-04-19 |
US20050187610A1 (en) | 2005-08-25 |
EP1233723A1 (en) | 2002-08-28 |
CA2386335A1 (en) | 2001-04-19 |
AU1199901A (en) | 2001-04-23 |
WO2001026583A1 (en) | 2001-04-19 |
CA2386335C (en) | 2008-12-30 |
US20020065549A1 (en) | 2002-05-30 |
JP2003523792A (en) | 2003-08-12 |
AU779189B2 (en) | 2005-01-13 |
US8721705B2 (en) | 2014-05-13 |
EP1233723A4 (en) | 2005-10-05 |
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