WO2009002631A1 - Endoprostheses for peripheral arteries and other body vessels - Google Patents
Endoprostheses for peripheral arteries and other body vessels Download PDFInfo
- Publication number
- WO2009002631A1 WO2009002631A1 PCT/US2008/063963 US2008063963W WO2009002631A1 WO 2009002631 A1 WO2009002631 A1 WO 2009002631A1 US 2008063963 W US2008063963 W US 2008063963W WO 2009002631 A1 WO2009002631 A1 WO 2009002631A1
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- WIPO (PCT)
- Prior art keywords
- stent
- strut member
- elongate strut
- connecting links
- adjacent
- Prior art date
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/91525—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other within the whole structure different bands showing different meander characteristics, e.g. frequency or amplitude
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/91533—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other characterised by the phase between adjacent bands
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/9155—Adjacent bands being connected to each other
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/9155—Adjacent bands being connected to each other
- A61F2002/91575—Adjacent bands being connected to each other connected peak to trough
Definitions
- the invention relates generally to vascular repair devices, and in particular to endoprostheses, more commonly referred to as intravascular stents, which are adapted to be implanted into a patient's body lumen, such as a blood vessel or artery, to maintain the patency thereof.
- Stents are particularly useful in the treatment of atherosclerotic stenosis in arteries and blood vessels.
- the present invention is directed to an intravascular stent that has a pattern or configuration that permits the stent to be placed in body vessels which are susceptible to physiological deformations and provides a high degree of fracture and fatigue resistance to such deformations.
- Peripheral Artery Disease is characterized by fatty plaque build-up in the arteries of the legs, which results in poor blood flow and circulation. Patients with PAD may experience muscle pain during walking, have wounds and ulcers that are slow to heal or, in the most severe cases, require amputation of the legs. Possible treatments for PAD include lifestyle modification (including cessation of smoking), medicines, balloon dilatation, metal stent placement or bypass surgery.
- Stents are generally tubular-shaped devices which function to hold open a segment of a blood vessel or other body lumen such as a coronary or peripheral artery. They also are suitable for use to support and hold back a dissected arterial lining that can occlude the fluid passageway.
- a coronary or peripheral artery a segment of a blood vessel or other body lumen
- a dissected arterial lining that can occlude the fluid passageway.
- stents there are numerous commercial stents being marketed throughout the world. While some of these stents are flexible and have the appropriate radial rigidity needed to hold open a vessel or artery, there typically is a tradeoff between flexibility and radial strength.
- Prior art stents typically fall into two general categories of construction.
- the first type of stent is expandable upon application of a controlled force, often through the inflation of the balloon portion of a dilatation catheter which, upon inflation of the balloon or other expansion means, expands the compressed stent to a larger diameter to be left in place within the artery at the target site.
- the second type of stent is a self-expanding stent formed from shape memory metals or super-elastic nickel-titanum (NiTi) alloys, which will automatically expand from a compressed state when the stent is advanced out of the distal end of the delivery catheter into the blood vessel.
- NiTi super-elastic nickel-titanum
- Stents can be implanted in the coronary arteries along with peripheral arteries, such as the renal arteries, the carotid arteries and in long arterial segments in the leg, all of which are susceptible to arteriosclerosis.
- peripheral arteries such as the renal arteries, the carotid arteries and in long arterial segments in the leg, all of which are susceptible to arteriosclerosis.
- balloon-expandable stents have been implanted in the coronary arteries since the coronary arteries are generally not vulnerable to bending and compression forces that can distort the stent structure.
- balloon-expandable stents are made from a stainless steel or cobalt- chromium alloy, multi-layer materials or other similar biocompatible materials.
- Peripheral vessels are usually more prone to natural bending and compressive forces which can easily bend and distort the implanted stent, causing it to fracture. For this reason, self-expanding stents are usually implanted in peripheral vessels since the self-expanding properties of the stent allows it to spring back to shape even after being subjected to bending or compressive forces.
- Peripheral stents can be much longer than coronary stents since longer segments of the peripheral artery are usually required to be treated.
- the current trend for manufacturing peripheral stents is moving towards a longer stent, typically about 80-120 mm and longer, to treat long arterial segments in patients with critical limb ischaemia (CLI) in such arteries as, for example, the superficial femoral artery (SFA), along with arteries below the knee.
- CLI critical limb ischaemia
- SFA superficial femoral artery
- Long segments of the peripheral arteries, such as the ilio-femoral-popliteal artery usually have regions where bending and compressive forces are so constant and repetitive that even a self-expanding stent can be subjected to possible deformation caused by fatigue and fracturing.
- the size of the body lumen can be quite small which prevents the use of some commercial stents which have profiles which are entirely too large to reach the small vessel.
- Many of these distal lesions are located deep within the tortuous vasculature of the patient which requires the stent to not only have a small profile, but also high flexibility to be advanced into these regions.
- the stent must be sufficiently flexible along its longitudinal axis, yet be configured to expand radially to provide sufficient strength and stability to maintain the patency of the body lumen.
- the stent and its delivery system must possess sufficient axial strength to achieve the needed pushability to maneuver the stent into the area of treatment.
- a stent which has a high degree of flexibility so that it can be advanced through tortuous passageways and can be radially expanded in a body segment which is susceptible to physiological deformations, and yet possesses sufficient mechanical strength to hold open the body lumen or artery to provide adequate vessel wall coverage while attaining a high degree of fracture and fatigue resistance.
- Such a stent should be able to match the physiological deformations associated in various regions of the body vessel to effectively provide a high level of fracture and fatigue resistance to the various loading conditions and deformation patterns to which the stent may be subjected.
- the present invention satisfies these and other needs.
- the present invention is directed to an intravascular stent that has a strut pattern or configuration that permits the stent to be placed in body vessels which are susceptible to certain physiological deformations and provides a high degree of fracture and fatigue resistance to the particular deformation.
- the stent is highly flexible along its longitudinal axis to facilitate delivery through tortuous body lumens, but is stiff and stable enough radially in its expanded condition to maintain the patency of a body lumen, such as an artery, when the stent is implanted therein.
- a composite stent made in accordance with the present invention can be formed with multiple stent segments, each stent segment have a different stent performance characteristic designed to match the physiological deformation present in the vessel segment in which that particular stent segment will be implanted.
- specific strut patterns can be created on specific stent segments to provide a high degree of fracture and fatigue resistance to a particular physiological deformation.
- stent segments with strut patterns which provide particularly high levels of fracture and fatigue resistance to torsional loading, bending loading or axial loading can be created and disposed along the length of the composite stent to match the type of loading to which the stent segment will be subjected.
- An axially or torsionally more flexible stent is likely to have lower stress when subjected to some deformation thereby producing enhanced resistance to deformation fracture or fatigue.
- a single composite stent having different performance characteristics can be created and implanted in long vessel segments, such as the ilio-femoral-popliteal arterial segment, to match the different physiological deformations encountered in each region of the arterial segment.
- a single stent segment could be manufactured into a single stent and implanted in a body vessel to provide the desired stent performance need for that particular body vessel.
- the present invention generally includes a plurality of elongate strut members that are spaced apart and extend along a longitudinal stent axis. These elongate strut members are interconnected to form a portion of the body of the stent.
- connecting links are integrally formed to connect adjacent elongate strut members together to cooperatively form the tubular stent body. These connecting links are designed to cause the elongate strut members to expand radially outward from a collapsed position to a radially expanded position. Not only do these connecting links provide flexibility and expandability to the stent body, but the positioning of the connecting links achieves different stent performance characteristics needed for a particular application.
- the particular stent pattern can be used individually to create a single stent or different stent segments having different performance characteristics can be combined to create a long, composite stent.
- each of the elongate strut members rings making up the stent has a proximal end and a distal end.
- the distal ends of the elongate strut members are connected together to form the distal end of the stent.
- the proximal ends of the elongate strut members are connected together to create the proximal end of the stent.
- each elongate strut member has a serpentine or undulating shape.
- the shape can be, for example, alternating peaks and valley which forms a sinusoidal wave.
- the undulating pattern of the elongate strut member can include U-shaped or V-shaped elements, although other shapes could be used as well.
- Each elongate strut member is connected to an adjacent elongate strut member by at least one connecting link.
- These connecting links are highly flexible and allow the stent to attain highly flexible along its longitudinal axis.
- the connecting links are disposed along the length of the stent in selective patterns which achieve and promote high levels of fracture and fatigue resistance for particular loading associated with different segments of a patient's vasculature.
- the connecting links are placed along the circumference of the stent body and align end to end in a "helix" pattern that winds around the stent body. This particular pattern of connecting links provide high fracture and fatigue resistance when the stent is subjected to torsional loading when implanted in the patient's vasculature.
- This particular pattern of connecting links results in a large expanded radius which results in stress being distributed over a greater area, resulting in less fatigue and less potential for stent fracture resulting from repetitive motion.
- This stent pattern provides excellent - - longitudinal flexibility while still providing good torsional flexibility once implanted in the patient.
- another strut pattern can be created by utilizing a set of connecting links placed along the body of the stent in a "stacked" configuration so that the connecting links are located laterally adjacent to each other in a plane that is substantially perpendicular to the stent longitudinal axis.
- each connecting link is disposed laterally adjacent to another to form a circumferential "ring-like" pattern which extends about the circumference of the stent body.
- This particular pattern of connecting links provides high fracture and fatigue resistance particularly when the stent is subjected to bending loading when implanted in the patient's vasculature.
- This particular pattern of connecting links also results in a concentration of stacked connecting links which increases the radial strength of the stent body and provides good flexibility.
- connecting links are placed along the body of the stent in an "offset-stacked" configuration, i.e., connecting links are placed on alternating elongated strut members and are aligned laterally adjacent to each other.
- there is an "offset” of connecting links which results in every other connecting link in the set remaining laterally aligned with another in a plane that is substantially perpendicular to the stent longitudinal axis.
- This particular pattern of connecting links provides high fracture and fatigue resistance particularly when the stent is subjected to axial loading when implanted in the patient's vasculature.
- This particular pattern of connecting links results in a stent segment having radial strength and flexibility evenly distributed throughout the length of the stent.
- two or more stent segments having different stent performance characteristics can be combined to create a composite stent.
- Each stent segment can be formed with the particular pattern of connecting links described above, namely the helix pattern, the stacked pattern and offset-stacked pattern.
- a stent segment made with multiple sets of stacked connecting links could be combined with a stent segment having connecting links disposed in the pattern which forms the continuous helix. This allows the stent manufacturer to create a stent having the desired stent characteristics which will match the physiological deformation conditions in regions of the body vessel in which each stent segment will be implanted. It should be appreciated that numerous combinations of stent segments can be attained to create various composite stents having different stent performance characteristics associated with the different segments forming the stent.
- the elongate strut members are formed of a plurality of peaks and valley where the peaks of the elongate strut members are aligned with each other. Likewise, the valley portions of the elongate strut members align with each other.
- the term "in phase” is commonly used to describe this alignment of peaks and valleys between adjacent elongated strut members.
- at least one connecting link attaches each elongate strut member to an adjacent strut member so that at least a portion of the connecting link is positioned within one of the peaks and it attaches the peaks to an adjacent peak.
- the connecting links have a bend or curved portion that will expand when the restraint placed on the self- expanding stent body is removed to allow the stent body to expand radially outwardly.
- the connecting links expand, the overall longitudinal length of the stent generally remains virtually unchanged.
- the fact that the elongate strut members do not expand or contract when the stent is radially expanded maintains the overall length of the stent substantially the same whether in the unexpanded and expanded configurations. In other words, the stent should not substantially shorten upon expansion.
- the stent may be formed from a tube by laser cutting the pattern of elongate struts and links in the tube.
- the stent also may be formed by laser cutting a flat metal - - sheet in the pattern of the elongate struts and links, and then rolling the pattern into the shape of the tubular stent and providing a longitudinal weld to form the stent.
- the term adjacent may be used to define directly adjacent or indirectly adjacent.
- FIGURE 1 is an elevational view, partially in section, of one particular embodiment of a stent made in accordance with the present invention mounted on a stent delivery catheter and positioned within an artery.
- FIG. 2 is an elevational view, partially in section, similar to that shown in FIG. 1 wherein the stent is partially expanded within the artery, so that the stent contacts the arterial wall.
- FIG. 3 is an elevational view, partially in section, showing the expanded stent implanted within the artery after withdrawal of the stent delivery catheter.
- FIG. 4 is a schematic diagram which depicts an anterior view of the upper portion of the leg and the arterial structure found in this portion of the leg and the physio-mechanical environment in this arterial structure.
- FIG. 5 is a schematic diagram which depicts a posterior view of the upper portion of the leg and the arterial structure found in this portion of the leg and the physio-mechanical environment in this arterial structure.
- FIG. 6 is a plan view of a portion of the stent depicted in FIGS. 1-3.
- FIG. 7 is a perspective view of the stent of FIG. 6 in a fully expanded configuration.
- FIG. 8 is a plan view of a portion of the stent depicted in FIGS. 1-3.
- FIG. 9 is a plan view of another embodiment of a stent made in accordance with the present invention.
- FIG. 10 is a plan view of another embodiment of a stent made in accordance with the present invention.
- FIG. 11 is a plan view of another embodiment of a stent made in accordance with the present invention.
- FIG. 12 is a plan view of another embodiment of a stent made in accordance with the present invention.
- FIG. 13 is a plan view of another embodiment of a stent made in accordance with the present invention.
- FIG. 14 is a plan view of a portion of a stent pattern showing the undulating portions of the elongate struts having varying amplitude.
- FIG. 15 is a plan view of a portion of a stent pattern showing the undulating portions of the elongate struts having different amplitudes.
- the present invention stent improves on existing stents by providing a longitudinally flexible stent having a uniquely designed pattern which has a high degree of fracture and fatigue resistance when subjected to physiological deformations associated with some body vessels.
- the stent of the present invention also provides radial rigidity and a high degree of scaffolding of a vessel wall, such as a peripheral artery.
- FIGS. 1-3 depicts a stent 10 made in accordance with the present invention mounted on a conventional catheter assembly 12 used to deliver the stent 10 and implant it in a body lumen, such as a peripheral artery, a coronary artery or other vessel within the body.
- the catheter assembly 12 is configured to advance through the patient's vascular system by advancing the catheter assembly 12 over a guide wire 14 using well known methods associated with over- the -wire or rapid-exchange catheter systems.
- the catheter assembly 12 is a typical self- expanding catheter delivery system which includes an inner member 16 having a stent mounting region 18 upon which the stent 10 is mounted.
- the inner member 16 includes a guide wire lumen 20 which receives the guide wire 14 and allows at least the distal portion of the catheter assembly 12 to slide over the guide wire 14.
- the guide wire lumen 20 is sized for receiving various diameter guide wires to suit a particular application.
- the stent 10 is mounted on the stent mounting region 18 of the inner member 16 and is maintained in a delivery position by an outer member 22 having a retraining sheath 24 which extends over the stent 10 to maintain it in a collapsed position so that the stent 10 and catheter 12 present a low profile diameter for delivery through the peripheral arteries (or other vessels).
- Stent 10 is used to repair a diseased or damaged arterial wall which may include plaque 28 as shown in FIGS. 1-3, or a dissection, or a flap of the arterial wall which is sometimes found in the peripheral and coronary arteries and other vessels.
- the guide wire 14 is first advanced through the patient's vascular system by using well known methods so that the distal end of the guide wire 14 is advanced past the plaque or diseased area 28.
- the cardiologist may wish to perform an angioplasty procedure or other procedure (i.e., atherectomy) in order to open the vessel and remodel the diseased area.
- the stent delivery catheter assembly 12 is advanced over the guide wire 14 so that the stent 10 is positioned in the target area.
- the restraining sheath 24 of the outer member 22 can then be retracted using a proximal handle 30 (located outside of the patient) so that the stent 10 will gradually be uncovered, as depicted in FIG. 2, to allow it to expand radially outward until the stent 10 is fully apposed to the vessel wall as depicted on FIG. 3.
- the catheter 12 can then be withdrawn from the patient's vascular system.
- the guide wire 14 is typically left in the artery for possible post-dilatation procedures, if any, and subsequently is withdrawn from the patient's vascular system as well.
- a balloon catheter (not shown) can be used, if needed, to post-dilate the self-expanding stent 10. If the stent 10 is of the balloon-expandable variety, it can be delivered to the area of treatment using well known methods as well.
- the stent 10 serves to hold open the artery 26 after the catheter is withdrawn, as illustrated by FIG. 3. Due to the formation of the stent 10 in the shape of an elongate tubular member, the undulating components of the stent 10 are relatively flat in transverse cross-section, so that when the stent is expanded, it is pressed into the wall of the artery and as a result does not interfere with the blood flow through the artery. The stent 10 is pressed into the wall of the artery and may eventually be covered with endothelial cell growth which further minimizes blood flow interference. The undulating portion of the stent provides good tacking characteristics to prevent stent movement within the artery. Furthermore, the closely spaced connecting links found at regular intervals along the length of the stent provide uniform support for the wall of the artery, as illustrated in FIG. 3.
- FIGS. 4-5 schematic diagrams depict the anterior and posterior view of the upper portion of a human leg and the arterial structure found in this portion of the leg.
- This particular arterial segment is a prime site for implanting a stent made in accordance with the present invention. It has been demonstrated that ilio- femoral-popliteal arterial segment undergo non-pulsatile deformations. These deformations have further been identified to be axial, torsional and/or bending. Furthermore, specific segments of the superficial femoral artery can be associated with specific non-pulsatile deformation.
- the proximal superficial femoral artery is subject to bending caused by movement of the leg.
- the proximal superficial femoral artery is subject to kinking at particular spots (identified by arrows in the top box) when the leg undergoes extension or flexion.
- This particular segment of the ilio- femoral-popliteal anatomy will be subject to continuous bending and kinking as the patient walks or runs. Accordingly, any stent implanted in this particular segment of the anatomy may be subject to the same kinking and bending experienced by this particular arterial segment.
- the mid proximal superficial femoral artery is subject to a different type of physiological deformation, namely, torsional loading, which can cause this arterial segment to become compressed.
- the distal superficial femoral artery shown near the knee joint, can be easily immobilized by the adductor canal which can cause unwanted axial loading on any stent implanted in this arterial segment.
- FIG. 5 the posterior view of the leg shows the femoral- popliteal segment below the adductor hiatus subject to bending or kinking as the leg moves. Kinking and bending of this arterial segment occurs, for example, when the leg undergoes 70% flexion. Any kinking or bending of the femoral-popliteal segment will likewise cause bending or kinking of any stent implanted in this particular arterial segment.
- FIGS. 6-15 depict the stent in various embodiments.
- FIGS. 6 and 8-13 show the stent in a flattened condition so that the pattern can be clearly viewed, even though the stent is in a cylindrical form in use, such as shown in FIG. 7.
- the stent is typically formed from a tubular member, however, it can be formed from a flat sheet and rolled into a cylindrical configuration.
- the particular strut patterns used to create the stent 10 are shown in the form of two stent segments A and B which combine together to create the long, composite stent 10.
- Each stent segment A and B has different stent performance characteristics than the other to allow the particular stent segment to be implanted in a particular portion of an arterial segment.
- the composite stent 10 can be fabricated using two or more stent segments having different stent performance characteristics to match the physiological deformations associated with the arterial segments in which the particular stent segments will be implanted. As a result, a composite stent having different regions of stent performance can be manufactured.
- Each individual stent segment can be made with a particular strut pattern which will provide high fracture and fatigue resistance under the loading condition and deformation patterns associated with the arterial segment in which the stent segment is implanted.
- the stent 10 includes a number of elongate strut members 32 which are spaced apart and extend along lengthwise to define a longitudinal stent axis. These elongated strut members 32 are interconnected with each other utilizing connecting links 34 which cooperatively form the tubular stent body. These connecting links 34 are designed to cause the elongate strut members 32 to expand radially outward from a collapsed position having a delivery diameter to a radially expanded position having an expanded diameter.
- connecting links 34 provide flexibility and expandability to the stent body, and the positioning of the connecting links 34 relative to each other achieves different stent performance characteristics. As will be explained below, the particular positioning of the connecting links 34 along the stent body achieves fatigue and fracture resistance in a response to the different physiological deformations associated with different arterial segment of the patient's vasculature.
- each elongated strut member 32 has a proximal end 36 and a distal end 38 which defines the longitudinal length of the stent body.
- Each of the distal ends 38 of the elongated strut members 32 are attached and form the distal end 40 of the stent body.
- the proximal ends 36 of each elongated strut member 32 are likewise attached to form the proximal end 42 of the stent.
- the proximal and distal ends of the elongated strut members could be attached to an expandable ring which would provide a more uniform edge for the ends of the stent.
- Stent segment A is shown in greater detail in FIGS. 6-7.
- FIG. 6 is a plan view of stent segment A with the structure flattened out into two dimensions to facilitate explanation.
- FIG. 7 shows stent segment B is an expanded perspective view.
- the elongated strut members 32 have a serpentine or undulating pattern. This undulating shape can be, for example, alternating peaks 44 and valleys 46 as shown in FIGS. 1-3 and 6-7.
- the peaks 44 and valley 46 can have many shapes including U-shapes, V-shapes, C-shapes, W-shapes or irregular radii-of-curvature-shapes, as disclosed in FIGS. 14 and 15 and discussed in greater detail below.
- Some of the peaks 44 on each elongate strut member are connected to a connecting link which is in turn connected to an adjacent elongate strut member.
- the elongate strut members and connecting links cooperatively form the tubular- shaped stent body.
- the number of peaks and valleys will depend upon the particular physical characteristics desired, along with the particular application to which the stent will be used.
- FIGS. 1-3 and 6-7 show the elongate strut members 32 having a plurality of alternating peaks 44 and valleys 46 wherein the peaks 44 of each elongate strut member are aligned with the peaks of the adjacent elongate strut members. Likewise, the valley portions 46 of each elongate strut member align with the valleys 46 of the adjacent elongate strut members.
- the connecting links 34 connect adjacent elongate strut members such that an end 48 of the connecting link 34 is attached to the elongate strut members so that at least a portion of the connecting link 34 is positioned within one of the peaks 44 of that elongate strut member 32.
- the other end 50 of the connecting link 34 is attached, in turn, to a peak 44 of an adjacent elongated strut member.
- the connecting link 34 does not connect peaks 44 of adjacent elongated strut members which are in phase with each, but rather, attaches peaks that are offset from each other.
- each connecting link 34 which attaches adjacent elongated strut members together are aligned end 48 to end 50 to create a helix pattern 52 which extends around the circumference of stent segment A. Dotted lines in FIG. 6 which shows the alignment of the connecting links which results in the formation of the helix pattern 52. It should be appreciated that only one side of the stent is shown in FIG. 6-7 and that the helix pattern repeats on the backside of the stent (not shown) to create a continuous helix along the entire length of the stent segment.
- stent segment A may include one or more helical patterns which extend around the circumference of the stent to attain the stent characteristics associated with this pattern.
- This particular stent pattern of stent segment A provides high fracture and fatigue resistant when the stent is subjected to torsional loading when placed in the patient's vasculature.
- This particular helix pattern of connecting links results in a large expanded radius allowing stress to be distributed over a greater area, thus resulting in less fatigue to the stent.
- This helical stent pattern provides excellent longitudinal flexibility while still providing good torsional flexibility once implanted in the patient.
- Stent segment A is particular suitable to be implanted arterial segments which are susceptible to torsional loading.
- stent segment A would be particularly suitable for implanting in the mid proximal superficial femoral artery which is subject to compression loading.
- the continuous helical pattern of connecting links provides the needed structure which helps to prevent fracture and fatigue once stent segment A is implanted in this arterial segment.
- stent segment B which forms part of the composite stent 10 of FIGS. 1-3 is shown in greater detail.
- a set of connecting links are placed along the stent body in a "stacked" configuration in which connecting links 34 are located laterally adjacent to each other in a plane that is substantially perpendicular to the stent longitudinal axis.
- Dotted lines define the stacked configuration S which results in the connecting links 34 being positioned directly laterally adjacent to each other to form a ring-like pattern that extends around the circumference of the stent body.
- Dotted lines also define a flex region F in which connecting links are missing to provide additional flexibility to stent segment B. As can be seen in FIGS.
- connecting links are placed in the stacked configuration to create additional regions of high radial strength along the length of stent segment B.
- These alternating sets of stacked connecting links provide a stent pattern having increased radial strength but possessing a bit less flexibility than stent segment A.
- the stack configuration of connecting links provides an area of radial strength which is particular suitable to resisting bending fatigue and fracture resulting when stent segment B is implanted in an arterial segment that is prone to continuous bending or kinking.
- this "stacked" configuration of connecting links provide superior radial force and strength which helps to prevent stent segment B from fatiguing and fracturing when subjected to the bending or kinking associated with an arterial segment such as the proximal superficial femoral artery or the distal femoral-popliteal segment - -
- the composite stent shown in FIGS. 1-3 is just one of the numerous combination of stent segments that can be achieved by the present invention. Accordingly, a composite stent including two or more stent segments can be manufactured to be implanted in a long arterial segment having different physiological deformations. It should be appreciated that although only two segments are shown connected to form the stent of FIGS. 1-3, more than two stent segments can be combined (as disclosed in other embodiments described below) to form a long stent body which matches particular stent segments to particular arterial segments. Also, the lengths and diameters (delivery diameter and expanded diameter) of the various segments can be varied, as needed, to create the appropriate length and radial size need for a given application.
- Stent segment C is a variation of the "stack" configuration of stent segment B as shown in FIG. 8.
- every other horizontal row of connecting links 34 in stent segment C is offset from another.
- alternating elongate strut members 32 are connected by connecting links 34 such that the connecting links are positioned laterally adjacent to each other in a plane that is substantially perpendicular to the longitudinal stent axis.
- dotted lines depict the alignment of alternating connecting links stacked adjacent to each other.
- This pattern differs from the "stacked" pattern of stent segment B in that there are alternating missing connecting links in the "stack.” Accordingly, it is referred to a an "offset-stacked" configuration.
- this offset-stacked pattern does not attain the radial strength achieved with stent segment B, it nevertheless possesses sufficient radial strength to maintain the arterial wall in its expanded condition.
- flexibility along stent segment C is increased compared to stent segment B.
- radial strength and flexibility can be evenly blended throughout the length of stent segment C.
- Stent segment C is particularly useful in providing high fracture and fatigue resistance to axial loading, which is associated with the distal superficial femoral artery. For this reason, stent segment C would be particularly useful in a arterial segment which undergoes significant axial loading.
- FIGS. 10-13 composite stents made from various combinations of the stent segments A, B and C are disclosed.
- a composite stent 50 made from stent segment B (FIG. 8) and segment C (FIG. 9) is shown.
- This composite stent 50 is particular suitable for implanting in a long arterial segment which is subject to bending or kinking and include a segment that is susceptible to axial loading. Accordingly, stent segment B would be implanted in the portion of the arterial segment which is susceptible to bending and kinking while stent segment C would be implanted in the portion of the arterial segment which is susceptible to axial deformation.
- FIG. 11 discloses a composite stent 60 created from the three stent segments A, B and C depicted in FIGS. 6-9.
- stent segment A consisting of the helix pattern (FIGS. 6-7) is combined with the stacked configuration of segment B and the offset-stacked pattern of stent segment C.
- FIG. 12 discloses a composite stent 70 made from stent segment A and stent segment B.
- the composite stent 80 depicted in FIG. 13 shows stent segment C located at ends of the composite stent 80 with stent segment B interposed between stent segments C.
- stent segments there are numerous other combinations which can be achieved utilizing the various stent segments disclosed herein. Additional, more than three stent segments could be connected together to match the physiological deformations that may be associated with a long length of an arterial segment. Additionally, as stated above, a stent could be made from only one of the stent segments A, B and C described above for implantation in a particular arterial segment.
- the composite stents disclosed herein are formed with elongate strut members which extend the entire length of the composite stent to define the longitudinal length of the composite stent.
- the stent patterns of the desired stent segment can be formed along the length of the elongate strut members to create the individual stent segment.
- the stent segments are spaced apart from each - - other by at least a pair of peaks and valleys which are free of any connection to a connecting link. It should be appreciated that a composite stent made in accordance with the present invention does not necessarily require the use of long elongate strut members to define the stent length. Rather, individual stent segments could be formed and connected together using one or more interconnecting members, such as connecting links.
- the size and shape of the undulating pattern of the elongated strut member 32 is shown having a non-uniform pattern.
- some of the valley portions 47 are larger in amplitude than other valley portions 46 to create a structure that has more scaffolding ability.
- the longer valley portions 47 can be used to provide additional strut material in an area which may have some voids once expanded.
- This particular figure shows that the alternating peaks and valleys which form the elongate strut member does not have to be a uniform in amplitude (height or depth) but can be varied to have strut lengths which provide more scaffolding ability to the stent.
- the height or amplitude of the peaks of the elongated strut members could be varied, as needed, to provide additional scaffolding to the composite stent.
- the stent pattern shows the elongate members having different amplitudes to also provide additional scaffolding to the stent.
- the amplitude of the undulating portion of several elongated strut members 33 are larger than adjacent elongated strut members 32 in order to provide more strut material to increase the scaffolding ability of the stent.
- the use of non-uniform shapes to create the peaks and valleys of the elongate strut members can allow for more even distribution of struts along the circumference of the stent body. It would be appreciated those skilled in the art that various forms of undulating patterns could be utilized in accordance with the present invention to create unique patterns to the elongated members in order to provide additional scaffolding to the stent.
- a suitable composition of Nitinol used in the manufacture of a self- expanding stent of the present invention is approximately 55% nickel and 44.5% titanium (by weight) with trace amounts of other elements making up about 0.5% of the composition. It should be appreciated that other compositions of Nitinol can be utilized, such as a nickel-titanium-platinum alloy, to obtain the same features of a self- expanding stent made in accordance with the present invention.
- the stent of the present invention can be laser cut from a tube of nickel titanium (Nitinol). All of the stent diameters can be cut with the same stent pattern, and the stent is expanded and heat treated to be stable at the desired final diameter.
- the heat treatment also controls the transformation temperature of the Nitinol such that the stent is superelastic at body temperature.
- the transformation temperature is at or below body temperature so that the stent will be superelastic at body temperature.
- the stent can be electro- polished to obtain a smooth finish with a thin layer of titanium oxide placed on the surface.
- the stent is usually implanted into the target vessel which is smaller than the stent diameter so that the stent applies a force to the vessel wall to keep it open.
- the stent tubing of a stent made in accordance with the present invention may be made of suitable biocompatible material besides nickel-titanium (NiTi) alloys. It should be appreciated the stent patterns of the present invention also can be used with balloon expandable stents as well. In this case, the stent would be formed using known techniques for manufacturing balloon expandable stents as well.
- the tubing may be made, for example, a suitable biocompatible material such as stainless steel.
- the stainless steel tube may be alloy-type: 316L SS, Special Chemistry per ASTM F138- 92 or ASTM F 139-92 grade 2.
- the stent of the present invention also can be made from a metallic material or an alloy such as, but not limited to, cobalt chromium alloy (ELGILOY), MP35N, MP20N, ELASTINITE, tantalum, platinum-iridium alloy, gold, magnesium, or combinations thereof.
- MP35N and MP20N are trade names for alloys of cobalt, nickel, chromium and molybdenum available from Standard Press Steel Co., Jenkintown, Pa.
- MP35N consists of 35% nickel, 20% chromium, and 120% molybdenum.
- MP20N consists of 50% cobalt, 20% nickel, 20% chromium, and 20% molybdenum.
- Stents also can be made from bioabsorbable or biostable polymers.
- One method of making the stent is to cut a thin-walled tubular member, such as Nitinol tubing, and remove portions of the tubing in the desired pattern for the stent, leaving relatively untouched the portions of the metallic tubing which are to form the stent.
- the tubing can be cut in the desired pattern by means of a machine-controlled laser.
- the tubing is put in a rotatable collet fixture of a machine-controlled apparatus for positioning the tubing relative to a laser. According to machine-encoded instructions, the tubing is then rotated and moved longitudinally relative to the laser which is also machine-controlled. The laser selectively removes the material from the tubing by ablation and a pattern is cut into the tube. The tube is therefore cut into the discrete pattern of the finished stent. Further details on how the tubing can be cut by a laser are found in U.S. Patent Nos. 5,759,192 (Saunders), 5,780,807 (Saunders) and 6,131,266 (Saunders), which are incorporated herein in their entirety.
- the process of cutting a pattern for the stent into the tubing generally is automated except for loading and unloading the length of tubing.
- a pattern can be cut in tubing using a CNC-opposing collet fixture for axial rotation of the length of tubing, in conjunction with CNC X/Y table to move the length of tubing axially relative to a machine-controlled laser as described.
- the entire space between collets can be patterned using the CO 2 or Nd:YAG laser set-up.
- the program for control of the apparatus is dependent on the particular configuration used and the pattern to be ablated in the coding.
- electrical chemical polishing using various techniques known in the art, should be employed in order to create the desired final polished finish for the stent.
- the electropolishing will also be able to take off protruding edges and rough surfaces which were created during the laser cutting procedure.
- any of the stents disclosed herein can be coated with a drug for treating the vascular system.
- the drug, therapeutic substance or active agent, terms which are used interchangeably, in the coating can inhibit the activity of vascular smooth muscle cells. More specifically, the active agent can be aimed at inhibiting abnormal or inappropriate migration and/or proliferation of smooth muscle cells for the inhibition of restenosis.
- the active agent can also include any substance capable of exerting a therapeutic or prophylactic effect for a diseased condition.
- the agent can be for enhancing wound healing in a vascular site or improving the structural and elastic properties of the vascular site.
- agents include antiproliferative substances such as actinomycin D, or derivatives and analogs thereof (manufactured by Sigma-Aldrich, Inc., Milwaukee, Wis.; or COSMEGEN available from Merck & Co., Inc., Whitehorse Station, NJ.). Synonyms of actinomycin D include dactinomycin, actinomycin IV, actinomycin I 1 , actinomycin X 1 , and actinomycin C 1 .
- the active agent can also fall under the genus of antineoplastic, anti-inflammatory, antiplatelet, anticoagulant, antifibrin, antithrombin, antimitotic, antibiotic, antiallergic and antioxidant substances.
- antineoplastics and/or antimitotics examples include paclitaxel (e.g., TAXOL® by Bristol-Myers Squibb Co., Stamford, Conn.), docetaxel (e.g., Taxotere®, from Aventis S.A., Frankfurt, Germany), methotrexate, azathioprine, vincristine, vinblastine, fluorouracil, doxorubicin hydrochloride (e.g., Adriamycin® from Pharmacia & Upjohn, Peapack, NJ.), and mitomycin (e.g., Mutamycin® from Bristol-Myers Squibb Co.).
- paclitaxel e.g., TAXOL® by Bristol-Myers Squibb Co., Stamford, Conn.
- docetaxel e.g., Taxotere®, from Aventis S.A., Frankfurt, Germany
- methotrexate e.g., azathioprine
- antiplatelets examples include sodium heparin, low molecular weight heparins, heparinoids, hirudin, argatroban, forskolin, vapiprost, pro-arg- chloromethylketone (synthetic antithrombin), dipyridamole, flycoprotein Ilb/IIIa platelet membrane receptor antagonist antibody, recombinant hirudin, and thrombin inhibitors such as Angiomax a (Biogen, Inc., Cambridge, Mass.).
- cytostatic or antiproliferative agents include angiopeptin, angiotensin converting enzyme inhibitors such as captopril (e.g., Capoten® and Capozide® from Bristol- Myers Squibb Co.), cilazapril or lisinopril (e.g., Prinvil® and Prinzide® from Merck & Co., Inc.), calcium channel blockers (such as nifedipine), colchicine, fibroblast growth factor (FGF) antagonists, fish oil (omega 3-fatty acid), histamine antagonists, lovastatin (an inhibitor of HMG-CoA reductase, a cholesterol lowering drug, brand name Mevacor® from Merck & Co., Inc.), monoclonal antibodies (such as those specific for Platelet-Derived Growth Factor (PDGF) receptors), nitroprusside, phosphodiesterase inhibitors, prostaglandin inhibitors, suramin, serotonin blockers, steroids,
- Coating 20 can be made from any suitable biocompatible polymer, examples of which include ethylene vinyl alcohol copolymer (commonly known by the generic name EVOH or by the trade name EVAL); poly(hydroxyvalerate); poly (L-lactic acid); polycaprolactone; poly(lactide-co-gly-colide); poly(hydroxybutyrate); poly(hydroxybutyrate-co-valerate); polydioxanone; polyorthoester; polyanhydride; poly(glycolic acid); poly(D,L-lactic acid); poly(flycolic acid-co-trimethylene carbonate); polyphosphoester; poly-phosphoester urethane; poly(aminoacids); cyanoacrylates; poly(trimethylene carbonate); poly(iminocarbonate); copoly(ether- esters) (e.g., PEO/PLA); polyalkylene oxalates; poly-phosphazenes; biomolecules, such as fibrin, fibrinogen, cellulose
Abstract
An endoprostheses for implanting in a body lumen, such as a coronary artery, peripheral artery, or other body lumen includes a plurality of elongate strut members spaced apart and extending along a longitudinal axis, each elongate strut member having a plurality of alternating peaks and valley. At least one flexible connecting link connects each elongate strut member to an adjacent elongate strut member. The elongate strut members and connecting links forming a generally tubular stent body having a first delivery diameter and a second implanted diameter. The positioning of the connecting links along the stent body produces desired stent performance characteristics.
Description
ENDOPROSTHESES FOR PERIPHERAL ARTERIES AND OTHER BODY VESSELS
BACKGROUND OF THE INVENTION
The invention relates generally to vascular repair devices, and in particular to endoprostheses, more commonly referred to as intravascular stents, which are adapted to be implanted into a patient's body lumen, such as a blood vessel or artery, to maintain the patency thereof. Stents are particularly useful in the treatment of atherosclerotic stenosis in arteries and blood vessels. More particularly, the present invention is directed to an intravascular stent that has a pattern or configuration that permits the stent to be placed in body vessels which are susceptible to physiological deformations and provides a high degree of fracture and fatigue resistance to such deformations.
Peripheral Artery Disease, or PAD, is characterized by fatty plaque build-up in the arteries of the legs, which results in poor blood flow and circulation. Patients with PAD may experience muscle pain during walking, have wounds and ulcers that are slow to heal or, in the most severe cases, require amputation of the legs. Possible treatments for PAD include lifestyle modification (including cessation of smoking), medicines, balloon dilatation, metal stent placement or bypass surgery.
Stents are generally tubular-shaped devices which function to hold open a segment of a blood vessel or other body lumen such as a coronary or peripheral artery. They also are suitable for use to support and hold back a dissected arterial lining that can occlude the fluid passageway. At present, there are numerous commercial stents being marketed throughout the world. While some of these stents are flexible and have the appropriate radial rigidity needed to hold open a vessel or artery, there typically is a tradeoff between flexibility and radial strength.
Prior art stents typically fall into two general categories of construction. The first type of stent is expandable upon application of a controlled force, often through the inflation of the balloon portion of a dilatation catheter which, upon inflation of the balloon or other expansion means, expands the compressed stent to a larger diameter to be left in place within the artery at the target site. The second type of stent is a
self-expanding stent formed from shape memory metals or super-elastic nickel-titanum (NiTi) alloys, which will automatically expand from a compressed state when the stent is advanced out of the distal end of the delivery catheter into the blood vessel. Such stents manufactured from expandable heat sensitive materials usually allow for phase transformations of the material to occur, resulting in the expansion and contraction of the stent.
Stents can be implanted in the coronary arteries along with peripheral arteries, such as the renal arteries, the carotid arteries and in long arterial segments in the leg, all of which are susceptible to arteriosclerosis. Generally, balloon-expandable stents have been implanted in the coronary arteries since the coronary arteries are generally not vulnerable to bending and compression forces that can distort the stent structure. Typically, balloon-expandable stents are made from a stainless steel or cobalt- chromium alloy, multi-layer materials or other similar biocompatible materials. Peripheral vessels, on the other hand, are usually more prone to natural bending and compressive forces which can easily bend and distort the implanted stent, causing it to fracture. For this reason, self-expanding stents are usually implanted in peripheral vessels since the self-expanding properties of the stent allows it to spring back to shape even after being subjected to bending or compressive forces.
Peripheral stents can be much longer than coronary stents since longer segments of the peripheral artery are usually required to be treated. The current trend for manufacturing peripheral stents is moving towards a longer stent, typically about 80-120 mm and longer, to treat long arterial segments in patients with critical limb ischaemia (CLI) in such arteries as, for example, the superficial femoral artery (SFA), along with arteries below the knee. Long segments of the peripheral arteries, such as the ilio-femoral-popliteal artery, usually have regions where bending and compressive forces are so constant and repetitive that even a self-expanding stent can be subjected to possible deformation caused by fatigue and fracturing. Other regions of peripheral arteries are subject to compressive forces which can prevent the stent from possibly spring back to its open, expanded configuration which can lead to stent fracture as well. For example, it has been shown that the ilio-femoral-popliteal segment undergoes non-pulsatile deformations which will, in turn, act on any stent implanted
in this arterial segment. These deformations have been identified as being axial, torsional and/or bending and specific segments of the superficial femoral artery have been associated with specific non-pulsatile deformations. These deformations can impinge on the stent's ability to maintain these arteries in a fully opened position and can result in deformation and fracturing of the often intricate strut patterns. Moreover, while one stent pattern may be suitable for a particular segment of artery, the same stent pattern may not be suitable for implantation in an adjacent arterial segment if a different type of non-pulsatile deformation is present in the adjacent arterial segment.
In many procedures which utilize stents to maintain the patency of the patient's body lumen, the size of the body lumen can be quite small which prevents the use of some commercial stents which have profiles which are entirely too large to reach the small vessel. Many of these distal lesions are located deep within the tortuous vasculature of the patient which requires the stent to not only have a small profile, but also high flexibility to be advanced into these regions. As a result, the stent must be sufficiently flexible along its longitudinal axis, yet be configured to expand radially to provide sufficient strength and stability to maintain the patency of the body lumen. Moreover, the stent and its delivery system must possess sufficient axial strength to achieve the needed pushability to maneuver the stent into the area of treatment.
What has been needed and heretofore unavailable is a stent which has a high degree of flexibility so that it can be advanced through tortuous passageways and can be radially expanded in a body segment which is susceptible to physiological deformations, and yet possesses sufficient mechanical strength to hold open the body lumen or artery to provide adequate vessel wall coverage while attaining a high degree of fracture and fatigue resistance. Such a stent should be able to match the physiological deformations associated in various regions of the body vessel to effectively provide a high level of fracture and fatigue resistance to the various loading conditions and deformation patterns to which the stent may be subjected. The present invention satisfies these and other needs.
SUMMARY OF THE INVENTION
The present invention is directed to an intravascular stent that has a strut pattern or configuration that permits the stent to be placed in body vessels which are susceptible to certain physiological deformations and provides a high degree of fracture and fatigue resistance to the particular deformation. The stent is highly flexible along its longitudinal axis to facilitate delivery through tortuous body lumens, but is stiff and stable enough radially in its expanded condition to maintain the patency of a body lumen, such as an artery, when the stent is implanted therein.
A composite stent made in accordance with the present invention can be formed with multiple stent segments, each stent segment have a different stent performance characteristic designed to match the physiological deformation present in the vessel segment in which that particular stent segment will be implanted. Accordingly, specific strut patterns can be created on specific stent segments to provide a high degree of fracture and fatigue resistance to a particular physiological deformation. For example, stent segments with strut patterns which provide particularly high levels of fracture and fatigue resistance to torsional loading, bending loading or axial loading can be created and disposed along the length of the composite stent to match the type of loading to which the stent segment will be subjected. An axially or torsionally more flexible stent is likely to have lower stress when subjected to some deformation thereby producing enhanced resistance to deformation fracture or fatigue. A single composite stent having different performance characteristics can be created and implanted in long vessel segments, such as the ilio-femoral-popliteal arterial segment, to match the different physiological deformations encountered in each region of the arterial segment. Alternatively, in accordance with the present invention, a single stent segment could be manufactured into a single stent and implanted in a body vessel to provide the desired stent performance need for that particular body vessel.
The present invention generally includes a plurality of elongate strut members that are spaced apart and extend along a longitudinal stent axis. These elongate strut members are interconnected to form a portion of the body of the stent. In one embodiment, connecting links are integrally formed to connect adjacent elongate strut
members together to cooperatively form the tubular stent body. These connecting links are designed to cause the elongate strut members to expand radially outward from a collapsed position to a radially expanded position. Not only do these connecting links provide flexibility and expandability to the stent body, but the positioning of the connecting links achieves different stent performance characteristics needed for a particular application. As addressed above, the particular stent pattern can be used individually to create a single stent or different stent segments having different performance characteristics can be combined to create a long, composite stent.
Each of the elongate strut members rings making up the stent has a proximal end and a distal end. The distal ends of the elongate strut members are connected together to form the distal end of the stent. Likewise, the proximal ends of the elongate strut members are connected together to create the proximal end of the stent. In one aspect of the invention, each elongate strut member has a serpentine or undulating shape. The shape can be, for example, alternating peaks and valley which forms a sinusoidal wave. Generally, the undulating pattern of the elongate strut member can include U-shaped or V-shaped elements, although other shapes could be used as well.
Each elongate strut member is connected to an adjacent elongate strut member by at least one connecting link. These connecting links are highly flexible and allow the stent to attain highly flexible along its longitudinal axis. The connecting links are disposed along the length of the stent in selective patterns which achieve and promote high levels of fracture and fatigue resistance for particular loading associated with different segments of a patient's vasculature. In one embodiment, the connecting links are placed along the circumference of the stent body and align end to end in a "helix" pattern that winds around the stent body. This particular pattern of connecting links provide high fracture and fatigue resistance when the stent is subjected to torsional loading when implanted in the patient's vasculature. This particular pattern of connecting links results in a large expanded radius which results in stress being distributed over a greater area, resulting in less fatigue and less potential for stent fracture resulting from repetitive motion. This stent pattern provides excellent
- - longitudinal flexibility while still providing good torsional flexibility once implanted in the patient.
In another aspect of the present invention, another strut pattern can be created by utilizing a set of connecting links placed along the body of the stent in a "stacked" configuration so that the connecting links are located laterally adjacent to each other in a plane that is substantially perpendicular to the stent longitudinal axis. In this particular configuration, each connecting link is disposed laterally adjacent to another to form a circumferential "ring-like" pattern which extends about the circumference of the stent body. This particular pattern of connecting links provides high fracture and fatigue resistance particularly when the stent is subjected to bending loading when implanted in the patient's vasculature. This particular pattern of connecting links also results in a concentration of stacked connecting links which increases the radial strength of the stent body and provides good flexibility.
This stacked connecting link pattern described above can be varied to create yet another embodiment of a stent segment which achieves different stent performance characteristics. In this aspect of the invention, connecting links are placed along the body of the stent in an "offset-stacked" configuration, i.e., connecting links are placed on alternating elongated strut members and are aligned laterally adjacent to each other. In this configuration, there is an "offset" of connecting links which results in every other connecting link in the set remaining laterally aligned with another in a plane that is substantially perpendicular to the stent longitudinal axis. This particular pattern of connecting links provides high fracture and fatigue resistance particularly when the stent is subjected to axial loading when implanted in the patient's vasculature. This particular pattern of connecting links results in a stent segment having radial strength and flexibility evenly distributed throughout the length of the stent.
In another aspect of the present invention, as addressed above, two or more stent segments having different stent performance characteristics (i.e. different connecting link patterns) can be combined to create a composite stent. Each stent segment can be formed with the particular pattern of connecting links described above, namely the helix pattern, the stacked pattern and offset-stacked pattern. For
example, in one particular embodiment, a stent segment made with multiple sets of stacked connecting links could be combined with a stent segment having connecting links disposed in the pattern which forms the continuous helix. This allows the stent manufacturer to create a stent having the desired stent characteristics which will match the physiological deformation conditions in regions of the body vessel in which each stent segment will be implanted. It should be appreciated that numerous combinations of stent segments can be attained to create various composite stents having different stent performance characteristics associated with the different segments forming the stent.
In another aspect of the present invention, the elongate strut members are formed of a plurality of peaks and valley where the peaks of the elongate strut members are aligned with each other. Likewise, the valley portions of the elongate strut members align with each other. The term "in phase" is commonly used to describe this alignment of peaks and valleys between adjacent elongated strut members. In this configuration, at least one connecting link attaches each elongate strut member to an adjacent strut member so that at least a portion of the connecting link is positioned within one of the peaks and it attaches the peaks to an adjacent peak.
While the elongate strut members and the connecting links generally are not separate structures, they have been conveniently referred to as elongate strut members and links for ease of identification. The number and location of connecting links can be varied as the application requires. In one embodiment, the connecting links have a bend or curved portion that will expand when the restraint placed on the self- expanding stent body is removed to allow the stent body to expand radially outwardly. When the connecting links expand, the overall longitudinal length of the stent generally remains virtually unchanged. The fact that the elongate strut members do not expand or contract when the stent is radially expanded maintains the overall length of the stent substantially the same whether in the unexpanded and expanded configurations. In other words, the stent should not substantially shorten upon expansion.
The stent may be formed from a tube by laser cutting the pattern of elongate struts and links in the tube. The stent also may be formed by laser cutting a flat metal
- - sheet in the pattern of the elongate struts and links, and then rolling the pattern into the shape of the tubular stent and providing a longitudinal weld to form the stent. As used throughout the present application, the term adjacent may be used to define directly adjacent or indirectly adjacent.
Other features and advantages of the present invention will become more apparent from the following detailed description of the invention when taken in conjunction with the accompanying exemplary drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
FIGURE 1 is an elevational view, partially in section, of one particular embodiment of a stent made in accordance with the present invention mounted on a stent delivery catheter and positioned within an artery.
FIG. 2 is an elevational view, partially in section, similar to that shown in FIG. 1 wherein the stent is partially expanded within the artery, so that the stent contacts the arterial wall.
FIG. 3 is an elevational view, partially in section, showing the expanded stent implanted within the artery after withdrawal of the stent delivery catheter.
FIG. 4 is a schematic diagram which depicts an anterior view of the upper portion of the leg and the arterial structure found in this portion of the leg and the physio-mechanical environment in this arterial structure.
FIG. 5 is a schematic diagram which depicts a posterior view of the upper portion of the leg and the arterial structure found in this portion of the leg and the physio-mechanical environment in this arterial structure.
FIG. 6 is a plan view of a portion of the stent depicted in FIGS. 1-3.
FIG. 7 is a perspective view of the stent of FIG. 6 in a fully expanded configuration.
FIG. 8 is a plan view of a portion of the stent depicted in FIGS. 1-3.
FIG. 9 is a plan view of another embodiment of a stent made in accordance with the present invention.
FIG. 10 is a plan view of another embodiment of a stent made in accordance with the present invention.
FIG. 11 is a plan view of another embodiment of a stent made in accordance with the present invention.
FIG. 12 is a plan view of another embodiment of a stent made in accordance with the present invention.
FIG. 13 is a plan view of another embodiment of a stent made in accordance with the present invention
FIG. 14 is a plan view of a portion of a stent pattern showing the undulating portions of the elongate struts having varying amplitude.
FIG. 15 is a plan view of a portion of a stent pattern showing the undulating portions of the elongate struts having different amplitudes.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
The present invention stent improves on existing stents by providing a longitudinally flexible stent having a uniquely designed pattern which has a high degree of fracture and fatigue resistance when subjected to physiological deformations associated with some body vessels. In addition to providing longitudinal flexibility, the stent of the present invention also provides radial rigidity and a high degree of scaffolding of a vessel wall, such as a peripheral artery.
Turning to the drawings, FIGS. 1-3 depicts a stent 10 made in accordance with the present invention mounted on a conventional catheter assembly 12 used to deliver the stent 10 and implant it in a body lumen, such as a peripheral artery, a coronary artery or other vessel within the body. The catheter assembly 12 is configured to advance through the patient's vascular system by advancing the catheter assembly 12 over a guide wire 14 using well known methods associated with over- the -wire or rapid-exchange catheter systems.
The catheter assembly 12, as depicted in FIGS. 1 and 2, is a typical self- expanding catheter delivery system which includes an inner member 16 having a stent mounting region 18 upon which the stent 10 is mounted. The inner member 16 includes a guide wire lumen 20 which receives the guide wire 14 and allows at least the distal portion of the catheter assembly 12 to slide over the guide wire 14. As is known in the art, the guide wire lumen 20 is sized for receiving various diameter guide wires to suit a particular application. The stent 10 is mounted on the stent
mounting region 18 of the inner member 16 and is maintained in a delivery position by an outer member 22 having a retraining sheath 24 which extends over the stent 10 to maintain it in a collapsed position so that the stent 10 and catheter 12 present a low profile diameter for delivery through the peripheral arteries (or other vessels).
As shown in FIG. 1, a partial cross-section of an artery 26 is shown with a small amount of plaque 28 that has been previously treated by an angioplasty or other repair procedure. Stent 10 is used to repair a diseased or damaged arterial wall which may include plaque 28 as shown in FIGS. 1-3, or a dissection, or a flap of the arterial wall which is sometimes found in the peripheral and coronary arteries and other vessels.
In a typical procedure to implant the self-expanding stent 10, the guide wire 14 is first advanced through the patient's vascular system by using well known methods so that the distal end of the guide wire 14 is advanced past the plaque or diseased area 28. Prior to implanting the stent 10, the cardiologist may wish to perform an angioplasty procedure or other procedure (i.e., atherectomy) in order to open the vessel and remodel the diseased area. Thereafter, the stent delivery catheter assembly 12 is advanced over the guide wire 14 so that the stent 10 is positioned in the target area. The restraining sheath 24 of the outer member 22 can then be retracted using a proximal handle 30 (located outside of the patient) so that the stent 10 will gradually be uncovered, as depicted in FIG. 2, to allow it to expand radially outward until the stent 10 is fully apposed to the vessel wall as depicted on FIG. 3. The catheter 12 can then be withdrawn from the patient's vascular system. The guide wire 14 is typically left in the artery for possible post-dilatation procedures, if any, and subsequently is withdrawn from the patient's vascular system as well. A balloon catheter (not shown) can be used, if needed, to post-dilate the self-expanding stent 10. If the stent 10 is of the balloon-expandable variety, it can be delivered to the area of treatment using well known methods as well.
The stent 10 serves to hold open the artery 26 after the catheter is withdrawn, as illustrated by FIG. 3. Due to the formation of the stent 10 in the shape of an elongate tubular member, the undulating components of the stent 10 are relatively flat in transverse cross-section, so that when the stent is expanded, it is pressed into the
wall of the artery and as a result does not interfere with the blood flow through the artery. The stent 10 is pressed into the wall of the artery and may eventually be covered with endothelial cell growth which further minimizes blood flow interference. The undulating portion of the stent provides good tacking characteristics to prevent stent movement within the artery. Furthermore, the closely spaced connecting links found at regular intervals along the length of the stent provide uniform support for the wall of the artery, as illustrated in FIG. 3.
Referring now to FIGS. 4-5, schematic diagrams depict the anterior and posterior view of the upper portion of a human leg and the arterial structure found in this portion of the leg. This particular arterial segment is a prime site for implanting a stent made in accordance with the present invention. It has been demonstrated that ilio- femoral-popliteal arterial segment undergo non-pulsatile deformations. These deformations have further been identified to be axial, torsional and/or bending. Furthermore, specific segments of the superficial femoral artery can be associated with specific non-pulsatile deformation. FIG. 4 shows the anterior view of the upper leg and the arterial structure which includes the femoral artery, the proximal superficial femoral artery, the mid proximal superficial femoral artery and the distal superficial femoral artery. As can be seen in the diagrams, the proximal superficial femoral artery, sometimes referred to as the ilio-femoral segment, is subject to bending caused by movement of the leg. As a result, the proximal superficial femoral artery is subject to kinking at particular spots (identified by arrows in the top box) when the leg undergoes extension or flexion. This particular segment of the ilio- femoral-popliteal anatomy will be subject to continuous bending and kinking as the patient walks or runs. Accordingly, any stent implanted in this particular segment of the anatomy may be subject to the same kinking and bending experienced by this particular arterial segment.
The mid proximal superficial femoral artery is subject to a different type of physiological deformation, namely, torsional loading, which can cause this arterial segment to become compressed. The distal superficial femoral artery, shown near the knee joint, can be easily immobilized by the adductor canal which can cause unwanted axial loading on any stent implanted in this arterial segment.
Referring now to FIG. 5, the posterior view of the leg shows the femoral- popliteal segment below the adductor hiatus subject to bending or kinking as the leg moves. Kinking and bending of this arterial segment occurs, for example, when the leg undergoes 70% flexion. Any kinking or bending of the femoral-popliteal segment will likewise cause bending or kinking of any stent implanted in this particular arterial segment.
In keeping with the present invention, FIGS. 6-15 depict the stent in various embodiments. FIGS. 6 and 8-13 show the stent in a flattened condition so that the pattern can be clearly viewed, even though the stent is in a cylindrical form in use, such as shown in FIG. 7. The stent is typically formed from a tubular member, however, it can be formed from a flat sheet and rolled into a cylindrical configuration.
Referring again to FIGS 1-3, the particular strut patterns used to create the stent 10 are shown in the form of two stent segments A and B which combine together to create the long, composite stent 10. Each stent segment A and B has different stent performance characteristics than the other to allow the particular stent segment to be implanted in a particular portion of an arterial segment. The composite stent 10 can be fabricated using two or more stent segments having different stent performance characteristics to match the physiological deformations associated with the arterial segments in which the particular stent segments will be implanted. As a result, a composite stent having different regions of stent performance can be manufactured. Each individual stent segment can be made with a particular strut pattern which will provide high fracture and fatigue resistance under the loading condition and deformation patterns associated with the arterial segment in which the stent segment is implanted.
Referring now to FIGS. 6-8, the particular stent patterns which forms the stent segments A and B are shown in greater detail. As can be seen from FIGS. 1-3 and 6- 8, the stent 10 includes a number of elongate strut members 32 which are spaced apart and extend along lengthwise to define a longitudinal stent axis. These elongated strut members 32 are interconnected with each other utilizing connecting links 34 which cooperatively form the tubular stent body. These connecting links 34 are designed to cause the elongate strut members 32 to expand radially outward from a collapsed
position having a delivery diameter to a radially expanded position having an expanded diameter. These connecting links 34 provide flexibility and expandability to the stent body, and the positioning of the connecting links 34 relative to each other achieves different stent performance characteristics. As will be explained below, the particular positioning of the connecting links 34 along the stent body achieves fatigue and fracture resistance in a response to the different physiological deformations associated with different arterial segment of the patient's vasculature.
As can be seen in FIGS. 1-6, each elongated strut member 32 has a proximal end 36 and a distal end 38 which defines the longitudinal length of the stent body. Each of the distal ends 38 of the elongated strut members 32 are attached and form the distal end 40 of the stent body. Likewise, the proximal ends 36 of each elongated strut member 32 are likewise attached to form the proximal end 42 of the stent. Alternatively, the proximal and distal ends of the elongated strut members could be attached to an expandable ring which would provide a more uniform edge for the ends of the stent. However, it is suitable for the ends of elongated strut members to be connected to each other to form the ends 40 and 42 of the stent.
Stent segment A is shown in greater detail in FIGS. 6-7. FIG. 6 is a plan view of stent segment A with the structure flattened out into two dimensions to facilitate explanation. FIG. 7 shows stent segment B is an expanded perspective view. In this particular embodiment of the present invention, the elongated strut members 32 have a serpentine or undulating pattern. This undulating shape can be, for example, alternating peaks 44 and valleys 46 as shown in FIGS. 1-3 and 6-7. The peaks 44 and valley 46, sometimes referred to as crests, curved portions, or irregular curved portions, can have many shapes including U-shapes, V-shapes, C-shapes, W-shapes or irregular radii-of-curvature-shapes, as disclosed in FIGS. 14 and 15 and discussed in greater detail below. Some of the peaks 44 on each elongate strut member are connected to a connecting link which is in turn connected to an adjacent elongate strut member. The elongate strut members and connecting links cooperatively form the tubular- shaped stent body. The number of peaks and valleys will depend upon the particular physical characteristics desired, along with the particular application to which the stent will be used.
The particular strut pattern shown in FIGS. 1-3 and 6-7 show the elongate strut members 32 having a plurality of alternating peaks 44 and valleys 46 wherein the peaks 44 of each elongate strut member are aligned with the peaks of the adjacent elongate strut members. Likewise, the valley portions 46 of each elongate strut member align with the valleys 46 of the adjacent elongate strut members. The term "in phase" in commonly used to describe this alignment of peaks and valleys of adjacent elongated strut members.
As can be seen in FIG. 6-7, the connecting links 34 connect adjacent elongate strut members such that an end 48 of the connecting link 34 is attached to the elongate strut members so that at least a portion of the connecting link 34 is positioned within one of the peaks 44 of that elongate strut member 32. The other end 50 of the connecting link 34 is attached, in turn, to a peak 44 of an adjacent elongated strut member. As can be seen in FIG. 6, the connecting link 34 does not connect peaks 44 of adjacent elongated strut members which are in phase with each, but rather, attaches peaks that are offset from each other. In this fashion, a larger connecting link 34 can be formed which allows the composite stent body to more readily expand to its expanded diameter as is shown in FIG. 7. Moreover, as can be seen best in FIG. 6, each connecting link 34 which attaches adjacent elongated strut members together are aligned end 48 to end 50 to create a helix pattern 52 which extends around the circumference of stent segment A. Dotted lines in FIG. 6 which shows the alignment of the connecting links which results in the formation of the helix pattern 52. It should be appreciated that only one side of the stent is shown in FIG. 6-7 and that the helix pattern repeats on the backside of the stent (not shown) to create a continuous helix along the entire length of the stent segment. It should be also appreciated that additional helix patterns of connecting links can be found on stent segment A as well. This additional helix extends between the helix pattern outlined by the dotted lines in FIGS 6 and 7. For this reason, the stent segment may include one or more helical patterns which extend around the circumference of the stent to attain the stent characteristics associated with this pattern.
This particular stent pattern of stent segment A provides high fracture and fatigue resistant when the stent is subjected to torsional loading when placed in the
patient's vasculature. This particular helix pattern of connecting links results in a large expanded radius allowing stress to be distributed over a greater area, thus resulting in less fatigue to the stent. This helical stent pattern provides excellent longitudinal flexibility while still providing good torsional flexibility once implanted in the patient. Stent segment A is particular suitable to be implanted arterial segments which are susceptible to torsional loading. For example, stent segment A would be particularly suitable for implanting in the mid proximal superficial femoral artery which is subject to compression loading. The continuous helical pattern of connecting links provides the needed structure which helps to prevent fracture and fatigue once stent segment A is implanted in this arterial segment.
Referring now to FIG. 8, stent segment B which forms part of the composite stent 10 of FIGS. 1-3 is shown in greater detail. In this particular stent pattern, a set of connecting links are placed along the stent body in a "stacked" configuration in which connecting links 34 are located laterally adjacent to each other in a plane that is substantially perpendicular to the stent longitudinal axis. Dotted lines define the stacked configuration S which results in the connecting links 34 being positioned directly laterally adjacent to each other to form a ring-like pattern that extends around the circumference of the stent body. Dotted lines also define a flex region F in which connecting links are missing to provide additional flexibility to stent segment B. As can be seen in FIGS. 6 and 7, several sets of connecting links are placed in the stacked configuration to create additional regions of high radial strength along the length of stent segment B. These alternating sets of stacked connecting links provide a stent pattern having increased radial strength but possessing a bit less flexibility than stent segment A. However, the stack configuration of connecting links provides an area of radial strength which is particular suitable to resisting bending fatigue and fracture resulting when stent segment B is implanted in an arterial segment that is prone to continuous bending or kinking. In this regard, this "stacked" configuration of connecting links provide superior radial force and strength which helps to prevent stent segment B from fatiguing and fracturing when subjected to the bending or kinking associated with an arterial segment such as the proximal superficial femoral artery or the distal femoral-popliteal segment
- -
The composite stent shown in FIGS. 1-3 is just one of the numerous combination of stent segments that can be achieved by the present invention. Accordingly, a composite stent including two or more stent segments can be manufactured to be implanted in a long arterial segment having different physiological deformations. It should be appreciated that although only two segments are shown connected to form the stent of FIGS. 1-3, more than two stent segments can be combined (as disclosed in other embodiments described below) to form a long stent body which matches particular stent segments to particular arterial segments. Also, the lengths and diameters (delivery diameter and expanded diameter) of the various segments can be varied, as needed, to create the appropriate length and radial size need for a given application.
Referring now to FIG. 9, another embodiment of a stent segment C is shown. Stent segment C is a variation of the "stack" configuration of stent segment B as shown in FIG. 8. In this particular aspect of the invention, every other horizontal row of connecting links 34 in stent segment C is offset from another. As can be seen in FIG. 9, alternating elongate strut members 32 are connected by connecting links 34 such that the connecting links are positioned laterally adjacent to each other in a plane that is substantially perpendicular to the longitudinal stent axis. Again, dotted lines depict the alignment of alternating connecting links stacked adjacent to each other. This pattern differs from the "stacked" pattern of stent segment B in that there are alternating missing connecting links in the "stack." Accordingly, it is referred to a an "offset-stacked" configuration. As can be seen in FIG. 9, there are numerous offset- stacked sets of connecting links formed along the longitudinal length of the stent body. While this offset-stacked pattern does not attain the radial strength achieved with stent segment B, it nevertheless possesses sufficient radial strength to maintain the arterial wall in its expanded condition. However, due to this offset positioning of connecting links, flexibility along stent segment C is increased compared to stent segment B. As a result, radial strength and flexibility can be evenly blended throughout the length of stent segment C. Stent segment C is particularly useful in providing high fracture and fatigue resistance to axial loading, which is associated
with the distal superficial femoral artery. For this reason, stent segment C would be particularly useful in a arterial segment which undergoes significant axial loading.
Referring now to FIGS. 10-13, composite stents made from various combinations of the stent segments A, B and C are disclosed. Referring initially to FIG. 10, a composite stent 50 made from stent segment B (FIG. 8) and segment C (FIG. 9) is shown. This composite stent 50 is particular suitable for implanting in a long arterial segment which is subject to bending or kinking and include a segment that is susceptible to axial loading. Accordingly, stent segment B would be implanted in the portion of the arterial segment which is susceptible to bending and kinking while stent segment C would be implanted in the portion of the arterial segment which is susceptible to axial deformation.
FIG. 11 discloses a composite stent 60 created from the three stent segments A, B and C depicted in FIGS. 6-9. In this regard, stent segment A consisting of the helix pattern (FIGS. 6-7) is combined with the stacked configuration of segment B and the offset-stacked pattern of stent segment C. As a result, the composite stent 60 has three region of different stent performance characteristics that can be accordingly matched to particular arterial segments. FIG. 12 discloses a composite stent 70 made from stent segment A and stent segment B. The composite stent 80 depicted in FIG. 13 shows stent segment C located at ends of the composite stent 80 with stent segment B interposed between stent segments C. It should appreciated that there are numerous other combinations which can be achieved utilizing the various stent segments disclosed herein. Additional, more than three stent segments could be connected together to match the physiological deformations that may be associated with a long length of an arterial segment. Additionally, as stated above, a stent could be made from only one of the stent segments A, B and C described above for implantation in a particular arterial segment.
The composite stents disclosed herein are formed with elongate strut members which extend the entire length of the composite stent to define the longitudinal length of the composite stent. The stent patterns of the desired stent segment can be formed along the length of the elongate strut members to create the individual stent segment. Generally, as can be seen in FIGS. 9-13, the stent segments are spaced apart from each
- - other by at least a pair of peaks and valleys which are free of any connection to a connecting link. It should be appreciated that a composite stent made in accordance with the present invention does not necessarily require the use of long elongate strut members to define the stent length. Rather, individual stent segments could be formed and connected together using one or more interconnecting members, such as connecting links.
Referring now to FIGS. 14-15, the size and shape of the undulating pattern of the elongated strut member 32 is shown having a non-uniform pattern. As can be seen in FIG. 14, some of the valley portions 47 are larger in amplitude than other valley portions 46 to create a structure that has more scaffolding ability. The longer valley portions 47 can be used to provide additional strut material in an area which may have some voids once expanded. This particular figure shows that the alternating peaks and valleys which form the elongate strut member does not have to be a uniform in amplitude (height or depth) but can be varied to have strut lengths which provide more scaffolding ability to the stent. Likewise, the height or amplitude of the peaks of the elongated strut members could be varied, as needed, to provide additional scaffolding to the composite stent.
Referring now to FIG. 15, the stent pattern shows the elongate members having different amplitudes to also provide additional scaffolding to the stent. As can be seen in FIG. 15, the amplitude of the undulating portion of several elongated strut members 33 are larger than adjacent elongated strut members 32 in order to provide more strut material to increase the scaffolding ability of the stent. The use of non-uniform shapes to create the peaks and valleys of the elongate strut members can allow for more even distribution of struts along the circumference of the stent body. It would be appreciated those skilled in the art that various forms of undulating patterns could be utilized in accordance with the present invention to create unique patterns to the elongated members in order to provide additional scaffolding to the stent.
For ease of illustration, the present invention has been depicted in a flattened plan view in most of the drawing figures herein. It should be noted, however, that all of the embodiments depicted herein are cylindrically-shaped stents that are generally formed from tubing by laser cutting as described below.
A suitable composition of Nitinol used in the manufacture of a self- expanding stent of the present invention is approximately 55% nickel and 44.5% titanium (by weight) with trace amounts of other elements making up about 0.5% of the composition. It should be appreciated that other compositions of Nitinol can be utilized, such as a nickel-titanium-platinum alloy, to obtain the same features of a self- expanding stent made in accordance with the present invention.
The stent of the present invention can be laser cut from a tube of nickel titanium (Nitinol). All of the stent diameters can be cut with the same stent pattern, and the stent is expanded and heat treated to be stable at the desired final diameter. The heat treatment also controls the transformation temperature of the Nitinol such that the stent is superelastic at body temperature. The transformation temperature is at or below body temperature so that the stent will be superelastic at body temperature. The stent can be electro- polished to obtain a smooth finish with a thin layer of titanium oxide placed on the surface. The stent is usually implanted into the target vessel which is smaller than the stent diameter so that the stent applies a force to the vessel wall to keep it open.
The stent tubing of a stent made in accordance with the present invention may be made of suitable biocompatible material besides nickel-titanium (NiTi) alloys. It should be appreciated the stent patterns of the present invention also can be used with balloon expandable stents as well. In this case, the stent would be formed using known techniques for manufacturing balloon expandable stents as well. The tubing may be made, for example, a suitable biocompatible material such as stainless steel. The stainless steel tube may be alloy-type: 316L SS, Special Chemistry per ASTM F138- 92 or ASTM F 139-92 grade 2. The stent of the present invention also can be made from a metallic material or an alloy such as, but not limited to, cobalt chromium alloy (ELGILOY), MP35N, MP20N, ELASTINITE, tantalum, platinum-iridium alloy, gold, magnesium, or combinations thereof. MP35N and MP20N are trade names for alloys of cobalt, nickel, chromium and molybdenum available from Standard Press Steel Co., Jenkintown, Pa. MP35N consists of 35% nickel, 20% chromium, and 120% molybdenum. MP20N consists of 50% cobalt, 20% nickel, 20% chromium, and 20% molybdenum. Stents also can be made from bioabsorbable or biostable polymers.
One method of making the stent, however, is to cut a thin-walled tubular member, such as Nitinol tubing, and remove portions of the tubing in the desired pattern for the stent, leaving relatively untouched the portions of the metallic tubing which are to form the stent. The tubing can be cut in the desired pattern by means of a machine-controlled laser.
Generally, the tubing is put in a rotatable collet fixture of a machine-controlled apparatus for positioning the tubing relative to a laser. According to machine-encoded instructions, the tubing is then rotated and moved longitudinally relative to the laser which is also machine-controlled. The laser selectively removes the material from the tubing by ablation and a pattern is cut into the tube. The tube is therefore cut into the discrete pattern of the finished stent. Further details on how the tubing can be cut by a laser are found in U.S. Patent Nos. 5,759,192 (Saunders), 5,780,807 (Saunders) and 6,131,266 (Saunders), which are incorporated herein in their entirety.
The process of cutting a pattern for the stent into the tubing generally is automated except for loading and unloading the length of tubing. For example, a pattern can be cut in tubing using a CNC-opposing collet fixture for axial rotation of the length of tubing, in conjunction with CNC X/Y table to move the length of tubing axially relative to a machine-controlled laser as described. The entire space between collets can be patterned using the CO2 or Nd:YAG laser set-up. The program for control of the apparatus is dependent on the particular configuration used and the pattern to be ablated in the coding.
After the stent has been cut by the laser, electrical chemical polishing, using various techniques known in the art, should be employed in order to create the desired final polished finish for the stent. The electropolishing will also be able to take off protruding edges and rough surfaces which were created during the laser cutting procedure.
Any of the stents disclosed herein can be coated with a drug for treating the vascular system. The drug, therapeutic substance or active agent, terms which are used interchangeably, in the coating can inhibit the activity of vascular smooth muscle cells. More specifically, the active agent can be aimed at inhibiting abnormal or inappropriate migration and/or proliferation of smooth muscle cells for the inhibition
of restenosis. The active agent can also include any substance capable of exerting a therapeutic or prophylactic effect for a diseased condition. For example, the agent can be for enhancing wound healing in a vascular site or improving the structural and elastic properties of the vascular site. Examples of agents include antiproliferative substances such as actinomycin D, or derivatives and analogs thereof (manufactured by Sigma-Aldrich, Inc., Milwaukee, Wis.; or COSMEGEN available from Merck & Co., Inc., Whitehorse Station, NJ.). Synonyms of actinomycin D include dactinomycin, actinomycin IV, actinomycin I1, actinomycin X1, and actinomycin C1. The active agent can also fall under the genus of antineoplastic, anti-inflammatory, antiplatelet, anticoagulant, antifibrin, antithrombin, antimitotic, antibiotic, antiallergic and antioxidant substances. Examples of such antineoplastics and/or antimitotics include paclitaxel (e.g., TAXOL® by Bristol-Myers Squibb Co., Stamford, Conn.), docetaxel (e.g., Taxotere®, from Aventis S.A., Frankfurt, Germany), methotrexate, azathioprine, vincristine, vinblastine, fluorouracil, doxorubicin hydrochloride (e.g., Adriamycin® from Pharmacia & Upjohn, Peapack, NJ.), and mitomycin (e.g., Mutamycin® from Bristol-Myers Squibb Co.). Examples of such antiplatelets, anticoagulants, antifibrin, and antithrombins include sodium heparin, low molecular weight heparins, heparinoids, hirudin, argatroban, forskolin, vapiprost, pro-arg- chloromethylketone (synthetic antithrombin), dipyridamole, flycoprotein Ilb/IIIa platelet membrane receptor antagonist antibody, recombinant hirudin, and thrombin inhibitors such as Angiomax a (Biogen, Inc., Cambridge, Mass.). Examples of such cytostatic or antiproliferative agents include angiopeptin, angiotensin converting enzyme inhibitors such as captopril (e.g., Capoten® and Capozide® from Bristol- Myers Squibb Co.), cilazapril or lisinopril (e.g., Prinvil® and Prinzide® from Merck & Co., Inc.), calcium channel blockers (such as nifedipine), colchicine, fibroblast growth factor (FGF) antagonists, fish oil (omega 3-fatty acid), histamine antagonists, lovastatin (an inhibitor of HMG-CoA reductase, a cholesterol lowering drug, brand name Mevacor® from Merck & Co., Inc.), monoclonal antibodies (such as those specific for Platelet-Derived Growth Factor (PDGF) receptors), nitroprusside, phosphodiesterase inhibitors, prostaglandin inhibitors, suramin, serotonin blockers, steroids, thioprotease inhibitors, triazolopyrimidine (a PDGF antagonist), and nitric
oxide. An example of an antiallergic agent is permirolast potassium. Other therapeutic substances or agents which may be appropriate include alpha-interferon, genetically engineered epithelial cells, rapamycin and it derivatives and analogs, and dexamethasone.
Coating 20 can be made from any suitable biocompatible polymer, examples of which include ethylene vinyl alcohol copolymer (commonly known by the generic name EVOH or by the trade name EVAL); poly(hydroxyvalerate); poly (L-lactic acid); polycaprolactone; poly(lactide-co-gly-colide); poly(hydroxybutyrate); poly(hydroxybutyrate-co-valerate); polydioxanone; polyorthoester; polyanhydride; poly(glycolic acid); poly(D,L-lactic acid); poly(flycolic acid-co-trimethylene carbonate); polyphosphoester; poly-phosphoester urethane; poly(aminoacids); cyanoacrylates; poly(trimethylene carbonate); poly(iminocarbonate); copoly(ether- esters) (e.g., PEO/PLA); polyalkylene oxalates; poly-phosphazenes; biomolecules, such as fibrin, fibrinogen, cellulose, starch, collagen and hyaluronic acid; polyurethanes; silicones; polyesters; polyolefiins; polyisobutylene and ethylene - alphaolefm copolymers; acrylic polymers and copolymers; vinyl halide polymers and copolymers, such as polyvinyl chloride; polyvinyl ethers, such as polyvinyl methyl ether; polyvinylidene halides, such as polyvinylidene fluoride and polyvinylidene chloride; polyacrylonitrile; polyvinyl ketones, polyvinyl aromatics, such as polystyrene; polyvinyl esters, such as polyvinyl acetate; copolymers of vinyl monomers with each other and olefins, such as ethylenemethyl methacrylate copolymers, acrylonitrile-styrene copolymers, ABS resins, and ethylene -vinyl acetate copolymers; polyamides, such as Nylon 66 and polycaprolactam; alkyd resins; polycarbonates; polyoxymethylenes; polyimides; polyethers; epoxy resins; polyurethanes; rayon; rayon- triacetate; cellulose; cellulose acetate; cellulose butyrate; cellulose acetate butyrate; cellophane; cellulose nitrate; cellulose propionate; cellulose ethers; and carboxymethyl cellulose. Coating 20 can also be silicon foam, neoprene, santoprene, or closed cell foam.
Although the present invention has been described in terms of certain preferred embodiments, other embodiments that are apparent to those of ordinary skill in the art are also within the scope of the invention. Accordingly, the scope of the invention is
intended to be defined only by reference to the appended claims. While the dimensions, types of materials and coatings described herein are intended to define the parameters of the invention, they are by no means limiting and are exemplary embodiments.
Claims
1. A stent, comprising: a plurality of elongate strut members spaced apart and extending along a longitudinal axis, each elongate strut member having a plurality of alternating peaks and valley; and at least one flexible connecting link connecting each elongate strut member to an adjacent elongate strut member, the elongate strut members and connecting links forming a generally tubular stent body having a first delivery diameter and a second implanted diameter, some of the connecting links being disposed adjacent to each other circumferentially along the tubular stent body to form at least one continuous helix pattern which extends along the longitudinal length of the tubular member.
2. The stent of claim 1, wherein a plurality of connecting links connecting each elongate strut member to an adjacent elongate strut member.
3. The stent of claim 2, wherein some the connecting links are disposed adjacent to each other circumferentially along the tubular stent body to form a second continuous helix pattern which extends along the longitudinal length of the tubular member.
4. The stent of claim 1, wherein each of the connecting links have a first end attached to the peak of an elongate strut member and a second end attached to the peak of an adjacent elongate strut member.
5. The stent of claim 1, wherein each of the plurality of elongate strut members have a proximal end and a distal end, the proximal ends of the elongate strut members being attached to form the proximal end of the tubular stent body and the distal ends of the elongate strut members being attached to form the distal end of the tubular stent body.
6. The stent of claim 1, wherein some of the first ends of the connecting links are attached to the same peak as the second ends of adjacent connecting links to form to helix pattern on the stent body.
7. The stent of claim 1, wherein at least one connecting link attaches each elongate strut member to an adjacent elongate strut member so that at least a portion of the connecting link is positioned within the peak as it attaches that peak to a peak of an adjacent elongate strut member.
8. The stent of claim 1, wherein the peaks and valleys of each elongate strut member are in phase with the peaks and valleys of adjacent elongate members.
9. A stent, comprising: a plurality of elongate strut members spaced apart and extending along a longitudinal axis, each elongate strut member having a plurality of alternating peaks and valley; and at least one connecting link connecting an elongate strut member to an adjacent elongate strut member, the elongate strut members and connecting links forming a generally tubular member having a first delivery diameter and a second implanted diameter, the connecting links being disposed laterally adjacent to each other about the tubular stent body.
10. The stent of claim 9, wherein a plurality of connecting links connect each elongate strut member to an adjacent strut member, some of the connecting links being disposed laterally adjacent to each other along the tubular stent body to form a first set of connecting links and some of the connecting links being disposed laterally adjacent to each other along the tubular stent body to form a second set of connecting links.
11. The stent of claim 9, wherein each of the connecting links have a first end attached to the peak of an elongate strut member and a second end attached to the peak of an adjacent elongate strut member.
12. The stent of claim 11, wherein some of the peaks of each elongate strut member has a first end of a connecting link attached thereto and a second end of adjacent connecting link attached thereto.
13. The stent of claim 9, wherein at least one connecting link attaches each elongate strut member to an adjacent elongate strut member so that at least a portion of the connecting link is positioned within the peak as it attaches that peak to a peak of an adjacent elongate strut member.
14. The stent of claim 9, wherein the peaks and valleys of each elongate strut member are in phase with the peaks and valleys of adjacent elongate members. - ZO -
15. The stent of claim 9, further including a plurality of connecting links connecting each elongate strut member to an adjacent strut member, some of the connecting links being disposed laterally adjacent to each other along the tubular stent body to form a set of connecting links, wherein at least two sets of connecting links are formed on the stent body.
16. The stent of claim 15, wherein each connecting link attaches a peak of an elongate strut member to a peak of an adjacent elongate strut member and at least one valley portion on each elongate strut member is disposed between sets of connecting links.
17. A stent, comprising: a plurality of elongate strut members spaced apart and extending along a longitudinal axis, each elongate strut member having a plurality of alternating peaks and valley; and at least one connecting link connecting an elongate strut member to an adjacent elongate strut member, the elongate strut members and connecting links forming a generally tubular stent body having a first delivery diameter and a second implanted diameter, the connecting links on alternating elongated strut members being disposed laterally adjacent to each other about the stent body.
18. The stent of claim 17, wherein a plurality of connecting links connect each elongate strut member to an adjacent strut member, some of the connecting links being disposed laterally adjacent to each other along the tubular stent body to form a first set of connecting links and some of the connecting links being disposed laterally adjacent to each other along the tubular stent body to form a second set of connecting links.
19. The stent of claim 17, wherein each of the connecting links have a first end attached to the peak of an elongate strut member and a second end attached to the peak of an adjacent elongate strut member.
20. The stent of claim 19, wherein some of the peaks of each elongate strut member has a first end of a connecting link attached thereto and a second end of adjacent connecting link attached thereto.
21. The stent of claim 17, wherein at least one connecting link attaches each elongate strut member to an adjacent elongate strut member so that at least a portion of the connecting link is positioned within the peak as it attaches that peak to a peak of an adjacent elongate strut member.
22. The stent of claim 17, wherein the peaks and valleys of each elongate strut member are in phase with the peaks and valleys of adjacent elongate members.
23. The stent of claim 17, further including a plurality of connecting links connecting each elongate strut member to an adjacent strut member, some of the connecting links being disposed laterally adjacent to each other along the tubular stent body to form a set of connecting links, wherein at least two sets of connecting links are formed on the stent body.
24. The stent of claim 23, wherein each connecting link attaches a peak of an elongate strut member to a peak of an adjacent elongate strut member and at least one valley portion on each elongate strut member is disposed between sets of connecting links.
25. A composite stent, comprising: a plurality of elongate strut members spaced apart and extending along a longitudinal axis, each elongate strut member having a plurality of alternating peaks and valley; and a plurality of connecting links connecting each elongate strut member to an adjacent elongate strut member, the elongate strut members and connecting links forming a generally tubular stent body having a first delivery diameter and a second implanted diameter, wherein the connecting links are disposed on the stent body to create at least two stent segments, each stent segment having a particular pattern of connecting links disposed circumferentially along the stent body.
26. The stent of claim 25, wherein the pattern of connecting links are selected from the group of connecting patterns consisting of (a) connecting links disposed adjacent to each other circumferentially along the tubular stent body to form at least one continuous helix pattern which extends along the longitudinal length of the tubular member, (b) connecting links disposed laterally adjacent to each other about the tubular stent body and (c) connecting links on alternating elongate strut members disposed laterally adjacent to each other about the tubular stent body.
27. The stent of claim 25, further including a plurality of connecting links connecting each elongate strut member to an adjacent strut member, some of the connecting links being disposed laterally adjacent to each other along the tubular stent body to form a set of connecting links, wherein at least two sets of connecting links are formed on the stent body.
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Families Citing this family (26)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7867273B2 (en) * | 2007-06-27 | 2011-01-11 | Abbott Laboratories | Endoprostheses for peripheral arteries and other body vessels |
US9226813B2 (en) | 2007-12-26 | 2016-01-05 | Cook Medical Technologies Llc | Low profile non-symmetrical stent |
GB2476451A (en) | 2009-11-19 | 2011-06-29 | Cook William Europ | Stent Graft |
US8728145B2 (en) | 2008-12-11 | 2014-05-20 | Cook Medical Technologies Llc | Low profile non-symmetrical stents and stent-grafts |
US8574284B2 (en) * | 2007-12-26 | 2013-11-05 | Cook Medical Technologies Llc | Low profile non-symmetrical bare alignment stents with graft |
US9180030B2 (en) * | 2007-12-26 | 2015-11-10 | Cook Medical Technologies Llc | Low profile non-symmetrical stent |
US10898620B2 (en) * | 2008-06-20 | 2021-01-26 | Razmodics Llc | Composite stent having multi-axial flexibility and method of manufacture thereof |
US9757263B2 (en) | 2009-11-18 | 2017-09-12 | Cook Medical Technologies Llc | Stent graft and introducer assembly |
US10342699B2 (en) | 2012-08-03 | 2019-07-09 | J.D. Franco & Co., Llc | Systems and methods for treating eye diseases |
WO2017156333A1 (en) | 2016-03-09 | 2017-09-14 | J.D. Franco & Co. | Systems and methods for treating eye diseases using retrograde blood flow |
CN104869945A (en) * | 2012-10-22 | 2015-08-26 | 奥巴斯尼茨医学公司 | Medical device for implantation into luminal structures |
US9980835B2 (en) | 2013-10-22 | 2018-05-29 | Orbusneich Medical Inc. | Medical device for implantation into luminal structures incorporating corrugated structural elements |
JP5695259B1 (en) * | 2014-02-19 | 2015-04-01 | 株式会社World Medish | High flexibility stent |
EP3240507A4 (en) | 2014-12-29 | 2018-12-05 | Ocudyne LLC | Apparatus and method for treating eye diseases |
WO2018057854A1 (en) | 2016-09-24 | 2018-03-29 | J.D. Franco & Company | Systems and methods for single puncture percutaneous reverse blood flow |
US11278389B2 (en) | 2016-12-08 | 2022-03-22 | J.D. Franco & Co., Llc | Methods and devices for treating an eye using a filter |
CA3051126A1 (en) | 2017-01-25 | 2018-08-02 | Robert Vidlund | Blood vessel access and closure devices and related methods of use |
US10898212B2 (en) | 2017-05-07 | 2021-01-26 | J.D. Franco & Co., Llc | Devices and methods for treating an artery |
US10779929B2 (en) | 2017-10-06 | 2020-09-22 | J.D. Franco & Co., Llc | Treating eye diseases by deploying a stent |
US10398880B2 (en) | 2017-11-02 | 2019-09-03 | J.D. Franco & Co., Llc | Medical systems, devices, and related methods |
WO2019118374A1 (en) | 2017-12-12 | 2019-06-20 | Penumbra, Inc. | Vascular cages and methods of making and using the same |
US10758254B2 (en) | 2017-12-15 | 2020-09-01 | J.D. Franco & Co., Llc | Medical systems, devices, and related methods |
US11478249B2 (en) | 2018-02-23 | 2022-10-25 | J.D. Franco & Co., Llc | Ophthalmic artery therapy under reverse flow |
US20200016299A1 (en) * | 2018-07-12 | 2020-01-16 | Cook Medical Technologies Llc | Coated medical device and method of coating such a device |
US10792478B2 (en) | 2018-12-31 | 2020-10-06 | J.D. Franco & Co., Llc | Intravascular devices, systems, and methods to address eye disorders |
CN112386377A (en) * | 2020-11-30 | 2021-02-23 | 山东瑞安泰医疗技术有限公司 | Medicine-carrying type punctiform stent |
Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP1197189A2 (en) * | 2000-10-10 | 2002-04-17 | BIOTRONIK Mess- und Therapiegeräte GmbH & Co Ingenieurbüro Berlin | Stent |
Family Cites Families (531)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3952747A (en) * | 1974-03-28 | 1976-04-27 | Kimmell Jr Garman O | Filter and filter insertion instrument |
DE2821048C2 (en) | 1978-05-13 | 1980-07-17 | Willy Ruesch Gmbh & Co Kg, 7053 Kernen | Medical instrument |
NZ201207A (en) * | 1981-07-23 | 1984-11-09 | British Petroleum Co Plc | Zeolite-based catalyst production and use |
US4425908A (en) | 1981-10-22 | 1984-01-17 | Beth Israel Hospital | Blood clot filter |
US4643184A (en) * | 1982-09-29 | 1987-02-17 | Mobin Uddin Kazi | Embolus trap |
US4494531A (en) * | 1982-12-06 | 1985-01-22 | Cook, Incorporated | Expandable blood clot filter |
US4727873A (en) * | 1984-04-17 | 1988-03-01 | Mobin Uddin Kazi | Embolus trap |
DK151404C (en) * | 1984-05-23 | 1988-07-18 | Cook Europ Aps William | FULLY FILTER FOR IMPLANTATION IN A PATIENT'S BLOOD |
IT1176442B (en) * | 1984-07-20 | 1987-08-18 | Enrico Dormia | INSTRUMENT FOR THE EXTRACTION OF FOREIGN BODIES FROM THE BODY'S PHYSIOLOGICAL CHANNELS |
FR2573646B1 (en) * | 1984-11-29 | 1988-11-25 | Celsa Composants Electr Sa | PERFECTED FILTER, PARTICULARLY FOR THE RETENTION OF BLOOD CLOTS |
US4790813A (en) * | 1984-12-17 | 1988-12-13 | Intravascular Surgical Instruments, Inc. | Method and apparatus for surgically removing remote deposits |
FR2580504B1 (en) | 1985-04-22 | 1987-07-10 | Pieronne Alain | FILTER FOR THE PARTIAL AND AT LEAST PROVISIONAL INTERRUPTION OF A VEIN AND CATHETER CARRYING THE FILTER |
US4706671A (en) * | 1985-05-02 | 1987-11-17 | Weinrib Harry P | Catheter with coiled tip |
US4662885A (en) * | 1985-09-03 | 1987-05-05 | Becton, Dickinson And Company | Percutaneously deliverable intravascular filter prosthesis |
US4650466A (en) * | 1985-11-01 | 1987-03-17 | Angiobrade Partners | Angioplasty device |
US4790812A (en) * | 1985-11-15 | 1988-12-13 | Hawkins Jr Irvin F | Apparatus and method for removing a target object from a body passsageway |
US4723549A (en) * | 1986-09-18 | 1988-02-09 | Wholey Mark H | Method and apparatus for dilating blood vessels |
FR2606641B1 (en) * | 1986-11-17 | 1991-07-12 | Promed | FILTERING DEVICE FOR BLOOD CLOTS |
US4794928A (en) * | 1987-06-10 | 1989-01-03 | Kletschka Harold D | Angioplasty device and method of using the same |
US4873978A (en) * | 1987-12-04 | 1989-10-17 | Robert Ginsburg | Device and method for emboli retrieval |
FR2624747A1 (en) * | 1987-12-18 | 1989-06-23 | Delsanti Gerard | REMOVABLE ENDO-ARTERIAL DEVICES FOR REPAIRING ARTERIAL WALL DECOLLEMENTS |
US4921478A (en) * | 1988-02-23 | 1990-05-01 | C. R. Bard, Inc. | Cerebral balloon angioplasty system |
FR2632848A1 (en) * | 1988-06-21 | 1989-12-22 | Lefebvre Jean Marie | FILTER FOR MEDICAL USE |
US4832055A (en) * | 1988-07-08 | 1989-05-23 | Palestrant Aubrey M | Mechanically locking blood clot filter |
US4921484A (en) * | 1988-07-25 | 1990-05-01 | Cordis Corporation | Mesh balloon catheter device |
US5152777A (en) * | 1989-01-25 | 1992-10-06 | Uresil Corporation | Device and method for providing protection from emboli and preventing occulsion of blood vessels |
US4969891A (en) * | 1989-03-06 | 1990-11-13 | Gewertz Bruce L | Removable vascular filter |
DE8910603U1 (en) * | 1989-09-06 | 1989-12-07 | Guenther, Rolf W., Prof. Dr. | |
US5100425A (en) * | 1989-09-14 | 1992-03-31 | Medintec R&D Limited Partnership | Expandable transluminal atherectomy catheter system and method for the treatment of arterial stenoses |
US4997435A (en) * | 1989-09-25 | 1991-03-05 | Methodist Hospital Of Indiana Inc. | Percutaneous catheter with encapsulating receptacle |
US5092839A (en) * | 1989-09-29 | 1992-03-03 | Kipperman Robert M | Coronary thrombectomy |
AU6376190A (en) | 1989-10-25 | 1991-05-02 | C.R. Bard Inc. | Occluding catheter and methods for treating cerebral arteries |
US5421832A (en) | 1989-12-13 | 1995-06-06 | Lefebvre; Jean-Marie | Filter-catheter and method of manufacturing same |
US5071407A (en) * | 1990-04-12 | 1991-12-10 | Schneider (U.S.A.) Inc. | Radially expandable fixation member |
US5221261A (en) | 1990-04-12 | 1993-06-22 | Schneider (Usa) Inc. | Radially expandable fixation member |
US5158548A (en) * | 1990-04-25 | 1992-10-27 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
CA2048307C (en) | 1990-08-14 | 1998-08-18 | Rolf Gunther | Method and apparatus for filtering blood in a blood vessel of a patient |
US5108419A (en) * | 1990-08-16 | 1992-04-28 | Evi Corporation | Endovascular filter and method for use thereof |
US5160342A (en) * | 1990-08-16 | 1992-11-03 | Evi Corp. | Endovascular filter and method for use thereof |
US5100423A (en) * | 1990-08-21 | 1992-03-31 | Medical Engineering & Development Institute, Inc. | Ablation catheter |
US5064428A (en) * | 1990-09-18 | 1991-11-12 | Cook Incorporated | Medical retrieval basket |
US5053008A (en) * | 1990-11-21 | 1991-10-01 | Sandeep Bajaj | Intracardiac catheter |
US5695518A (en) | 1990-12-28 | 1997-12-09 | Laerum; Frode | Filtering device for preventing embolism and/or distension of blood vessel walls |
US5350398A (en) | 1991-05-13 | 1994-09-27 | Dusan Pavcnik | Self-expanding filter for percutaneous insertion |
EP0590050B1 (en) | 1991-06-17 | 1999-03-03 | Wilson-Cook Medical Inc. | Endoscopic extraction device having composite wire construction |
DE9109006U1 (en) | 1991-07-22 | 1991-10-10 | Schmitz-Rode, Thomas, Dipl.-Ing. Dr.Med., 5100 Aachen, De | |
US5192286A (en) * | 1991-07-26 | 1993-03-09 | Regents Of The University Of California | Method and device for retrieving materials from body lumens |
US5626605A (en) | 1991-12-30 | 1997-05-06 | Scimed Life Systems, Inc. | Thrombosis filter |
FR2689388B1 (en) | 1992-04-07 | 1999-07-16 | Celsa Lg | PERFECTIONALLY RESORBABLE BLOOD FILTER. |
US5324304A (en) * | 1992-06-18 | 1994-06-28 | William Cook Europe A/S | Introduction catheter set for a collapsible self-expandable implant |
US5527338A (en) * | 1992-09-02 | 1996-06-18 | Board Of Regents, The University Of Texas System | Intravascular device |
FR2696092B1 (en) | 1992-09-28 | 1994-12-30 | Lefebvre Jean Marie | Kit for medical use composed of a filter and its device for placement in the vessel. |
US5836868A (en) | 1992-11-13 | 1998-11-17 | Scimed Life Systems, Inc. | Expandable intravascular occlusion material removal devices and methods of use |
US5501694A (en) | 1992-11-13 | 1996-03-26 | Scimed Life Systems, Inc. | Expandable intravascular occlusion material removal devices and methods of use |
US5792157A (en) | 1992-11-13 | 1998-08-11 | Scimed Life Systems, Inc. | Expandable intravascular occlusion material removal devices and methods of use |
US5490859A (en) | 1992-11-13 | 1996-02-13 | Scimed Life Systems, Inc. | Expandable intravascular occlusion material removal devices and methods of use |
FR2699809B1 (en) | 1992-12-28 | 1995-02-17 | Celsa Lg | Device which can selectively constitute a temporary blood filter. |
DE69433774T2 (en) | 1993-02-19 | 2005-04-14 | Boston Scientific Corp., Natick | SURGICAL EXTRACTOR |
US5897567A (en) | 1993-04-29 | 1999-04-27 | Scimed Life Systems, Inc. | Expandable intravascular occlusion material removal devices and methods of use |
US5634942A (en) | 1994-04-21 | 1997-06-03 | B. Braun Celsa | Assembly comprising a blood filter for temporary or definitive use and a device for implanting it |
DE9409484U1 (en) | 1994-06-11 | 1994-08-04 | Naderlinger Eduard | Vena cava thrombus filter |
US6123715A (en) | 1994-07-08 | 2000-09-26 | Amplatz; Curtis | Method of forming medical devices; intravascular occlusion devices |
EP1695673A3 (en) | 1994-07-08 | 2009-07-08 | ev3 Inc. | Intravascular filtering device |
US5601595A (en) | 1994-10-25 | 1997-02-11 | Scimed Life Systems, Inc. | Remobable thrombus filter |
US5658296A (en) | 1994-11-21 | 1997-08-19 | Boston Scientific Corporation | Method for making surgical retrieval baskets |
US6013093A (en) | 1995-11-28 | 2000-01-11 | Boston Scientific Corporation | Blood clot filtering |
US5690671A (en) | 1994-12-13 | 1997-11-25 | Micro Interventional Systems, Inc. | Embolic elements and methods and apparatus for their delivery |
US5549626A (en) | 1994-12-23 | 1996-08-27 | New York Society For The Ruptured And Crippled Maintaining The Hospital For Special Surgery | Vena caval filter |
US6348056B1 (en) | 1999-08-06 | 2002-02-19 | Scimed Life Systems, Inc. | Medical retrieval device with releasable retrieval basket |
US6896696B2 (en) * | 1998-11-20 | 2005-05-24 | Scimed Life Systems, Inc. | Flexible and expandable stent |
DK0734698T4 (en) * | 1995-04-01 | 2006-07-03 | Variomed Ag | Stent for transluminal implantation in hollow organs |
US5795322A (en) | 1995-04-10 | 1998-08-18 | Cordis Corporation | Catheter with filter and thrombus-discharge device |
ES2206549T3 (en) | 1995-04-14 | 2004-05-16 | B. Braun Medical Sas | INSTRUMENTAL MEDICAL DEVICE SUCH AS SANGUINEO FILTER. |
US5681347A (en) | 1995-05-23 | 1997-10-28 | Boston Scientific Corporation | Vena cava filter delivery system |
US5833650A (en) | 1995-06-05 | 1998-11-10 | Percusurge, Inc. | Catheter apparatus and method for treating occluded vessels |
US20020193828A1 (en) | 2001-06-14 | 2002-12-19 | Cook Incorporated | Endovascular filter |
TW438587B (en) | 1995-06-20 | 2001-06-07 | Takeda Chemical Industries Ltd | A pharmaceutical composition for prophylaxis and treatment of diabetes |
FR2735967B1 (en) | 1995-06-27 | 1998-03-06 | Perouse Implant Lab | VASCULAR SURGERY TOOL AND ITS USE |
FR2737654B1 (en) | 1995-08-10 | 1997-11-21 | Braun Celsa Sa | FILTRATION UNIT FOR THE RETENTION OF BLOOD CLOTS |
US6168604B1 (en) | 1995-10-06 | 2001-01-02 | Metamorphic Surgical Devices, Llc | Guide wire device for removing solid objects from body canals |
US5779716A (en) | 1995-10-06 | 1998-07-14 | Metamorphic Surgical Devices, Inc. | Device for removing solid objects from body canals, cavities and organs |
US6264663B1 (en) | 1995-10-06 | 2001-07-24 | Metamorphic Surgical Devices, Llc | Device for removing solid objects from body canals, cavities and organs including an invertable basket |
US5989281A (en) | 1995-11-07 | 1999-11-23 | Embol-X, Inc. | Cannula with associated filter and methods of use during cardiac surgery |
US5769816A (en) | 1995-11-07 | 1998-06-23 | Embol-X, Inc. | Cannula with associated filter |
US5695519A (en) | 1995-11-30 | 1997-12-09 | American Biomed, Inc. | Percutaneous filter for carotid angioplasty |
US5938682A (en) * | 1996-01-26 | 1999-08-17 | Cordis Corporation | Axially flexible stent |
EP0879068A4 (en) | 1996-02-02 | 1999-04-21 | Transvascular Inc | Methods and apparatus for blocking flow through blood vessels |
US5895398A (en) | 1996-02-02 | 1999-04-20 | The Regents Of The University Of California | Method of using a clot capture coil |
NL1002423C2 (en) | 1996-02-22 | 1997-08-25 | Cordis Europ | Temporary filter catheter. |
US5846251A (en) | 1996-07-22 | 1998-12-08 | Hart; Charles C. | Access device with expandable containment member |
US5935139A (en) | 1996-05-03 | 1999-08-10 | Boston Scientific Corporation | System for immobilizing or manipulating an object in a tract |
US6800080B1 (en) | 1996-05-03 | 2004-10-05 | Scimed Life Systems, Inc. | Medical retrieval device |
US6096053A (en) | 1996-05-03 | 2000-08-01 | Scimed Life Systems, Inc. | Medical retrieval basket |
WO1997042879A1 (en) | 1996-05-14 | 1997-11-20 | Embol-X, Inc. | Aortic occluder with associated filter and methods of use during cardiac surgery |
US6652480B1 (en) | 1997-03-06 | 2003-11-25 | Medtronic Ave., Inc. | Methods for reducing distal embolization |
US6544276B1 (en) | 1996-05-20 | 2003-04-08 | Medtronic Ave. Inc. | Exchange method for emboli containment |
US6270477B1 (en) | 1996-05-20 | 2001-08-07 | Percusurge, Inc. | Catheter for emboli containment |
JP3690815B2 (en) | 1996-05-20 | 2005-08-31 | メドトロニック パークサージ インコーポレイテッド | Small section catheter |
US20050245894A1 (en) | 1996-05-20 | 2005-11-03 | Medtronic Vascular, Inc. | Methods and apparatuses for drug delivery to an intravascular occlusion |
US6022336A (en) | 1996-05-20 | 2000-02-08 | Percusurge, Inc. | Catheter system for emboli containment |
NL1003497C2 (en) | 1996-07-03 | 1998-01-07 | Cordis Europ | Catheter with temporary vena-cava filter. |
US5669933A (en) | 1996-07-17 | 1997-09-23 | Nitinol Medical Technologies, Inc. | Removable embolus blood clot filter |
US5662671A (en) | 1996-07-17 | 1997-09-02 | Embol-X, Inc. | Atherectomy device having trapping and excising means for removal of plaque from the aorta and other arteries |
US6066158A (en) | 1996-07-25 | 2000-05-23 | Target Therapeutics, Inc. | Mechanical clot encasing and removal wire |
US5807404A (en) * | 1996-09-19 | 1998-09-15 | Medinol Ltd. | Stent with variable features to optimize support and method of making such stent |
US6447530B1 (en) | 1996-11-27 | 2002-09-10 | Scimed Life Systems, Inc. | Atraumatic anchoring and disengagement mechanism for permanent implant device |
US5876367A (en) | 1996-12-05 | 1999-03-02 | Embol-X, Inc. | Cerebral protection during carotid endarterectomy and downstream vascular protection during other surgeries |
FR2758078B1 (en) | 1997-01-03 | 1999-07-16 | Braun Celsa Sa | BLOOD FILTER WITH IMPROVED PERMEABILITY |
US5776162A (en) | 1997-01-03 | 1998-07-07 | Nitinol Medical Technologies, Inc. | Vessel implantable shape memory appliance with superelastic hinged joint |
WO1998033443A1 (en) | 1997-02-03 | 1998-08-06 | Angioguard, Inc. | Vascular filter |
US6391044B1 (en) | 1997-02-03 | 2002-05-21 | Angioguard, Inc. | Vascular filter system |
US6295989B1 (en) | 1997-02-06 | 2001-10-02 | Arteria Medical Science, Inc. | ICA angioplasty with cerebral protection |
US20020169458A1 (en) | 1997-02-06 | 2002-11-14 | Connors John J. | ICA angioplasty with cerebral protection |
US5827321A (en) * | 1997-02-07 | 1998-10-27 | Cornerstone Devices, Inc. | Non-Foreshortening intraluminal prosthesis |
US6254633B1 (en) | 1997-02-12 | 2001-07-03 | Corvita Corporation | Delivery device for a medical device having a constricted region |
US5882329A (en) | 1997-02-12 | 1999-03-16 | Prolifix Medical, Inc. | Apparatus and method for removing stenotic material from stents |
JP2001512334A (en) | 1997-02-12 | 2001-08-21 | プロリフィックス メディカル,インコーポレイテッド | Equipment for removing material from stents |
US5800457A (en) | 1997-03-05 | 1998-09-01 | Gelbfish; Gary A. | Intravascular filter and associated methodology |
WO1998039053A1 (en) | 1997-03-06 | 1998-09-11 | Scimed Life Systems, Inc. | Distal protection device and method |
US6974469B2 (en) | 1997-03-06 | 2005-12-13 | Scimed Life Systems, Inc. | Distal protection device and method |
US5827324A (en) | 1997-03-06 | 1998-10-27 | Scimed Life Systems, Inc. | Distal protection device |
US6152946A (en) | 1998-03-05 | 2000-11-28 | Scimed Life Systems, Inc. | Distal protection device and method |
US7094249B1 (en) | 1997-03-06 | 2006-08-22 | Boston Scientific Scimed, Inc. | Distal protection device and method |
US5814064A (en) | 1997-03-06 | 1998-09-29 | Scimed Life Systems, Inc. | Distal protection device |
US5810872A (en) * | 1997-03-14 | 1998-09-22 | Kanesaka; Nozomu | Flexible stent |
US5772674A (en) | 1997-03-31 | 1998-06-30 | Nakhjavan; Fred K. | Catheter for removal of clots in blood vessels |
US6258115B1 (en) | 1997-04-23 | 2001-07-10 | Artemis Medical, Inc. | Bifurcated stent and distal protection system |
IT1292295B1 (en) * | 1997-04-29 | 1999-01-29 | Sorin Biomedica Cardio Spa | ANGIOPLASTIC STENT |
US6451049B2 (en) * | 1998-04-29 | 2002-09-17 | Sorin Biomedica Cardio, S.P.A. | Stents for angioplasty |
US5868708A (en) | 1997-05-07 | 1999-02-09 | Applied Medical Resources Corporation | Balloon catheter apparatus and method |
US5911734A (en) | 1997-05-08 | 1999-06-15 | Embol-X, Inc. | Percutaneous catheter and guidewire having filter and medical device deployment capabilities |
US5846260A (en) | 1997-05-08 | 1998-12-08 | Embol-X, Inc. | Cannula with a modular filter for filtering embolic material |
US6676682B1 (en) | 1997-05-08 | 2004-01-13 | Scimed Life Systems, Inc. | Percutaneous catheter and guidewire having filter and medical device deployment capabilities |
US6258120B1 (en) | 1997-12-23 | 2001-07-10 | Embol-X, Inc. | Implantable cerebral protection device and methods of use |
US5954745A (en) | 1997-05-16 | 1999-09-21 | Gertler; Jonathan | Catheter-filter set having a compliant seal |
US6761727B1 (en) | 1997-06-02 | 2004-07-13 | Medtronic Ave, Inc. | Filter assembly |
US6059814A (en) | 1997-06-02 | 2000-05-09 | Medtronic Ave., Inc. | Filter for filtering fluid in a bodily passageway |
US5913895A (en) * | 1997-06-02 | 1999-06-22 | Isostent, Inc. | Intravascular stent with enhanced rigidity strut members |
US5800525A (en) | 1997-06-04 | 1998-09-01 | Vascular Science, Inc. | Blood filter |
US5848964A (en) | 1997-06-06 | 1998-12-15 | Samuels; Shaun Lawrence Wilkie | Temporary inflatable filter device and method of use |
EP0890346A1 (en) * | 1997-06-13 | 1999-01-13 | Gary J. Becker | Expandable intraluminal endoprosthesis |
US5843175A (en) * | 1997-06-13 | 1998-12-01 | Global Therapeutics, Inc. | Enhanced flexibility surgical stent |
EP0884029B1 (en) * | 1997-06-13 | 2004-12-22 | Gary J. Becker | Expandable intraluminal endoprosthesis |
US6245088B1 (en) | 1997-07-07 | 2001-06-12 | Samuel R. Lowery | Retrievable umbrella sieve and method of use |
DE19834956B9 (en) * | 1997-08-01 | 2005-10-20 | Eckhard Alt | Supporting prosthesis (stent) |
US5941896A (en) | 1997-09-08 | 1999-08-24 | Montefiore Hospital And Medical Center | Filter and method for trapping emboli during endovascular procedures |
US6361545B1 (en) | 1997-09-26 | 2002-03-26 | Cardeon Corporation | Perfusion filter catheter |
US6395014B1 (en) | 1997-09-26 | 2002-05-28 | John A. Macoviak | Cerebral embolic protection assembly and associated methods |
US6174318B1 (en) | 1998-04-23 | 2001-01-16 | Scimed Life Systems, Inc. | Basket with one or more moveable legs |
US6099534A (en) | 1997-10-01 | 2000-08-08 | Scimed Life Systems, Inc. | Releasable basket |
US6183482B1 (en) | 1997-10-01 | 2001-02-06 | Scimed Life Systems, Inc. | Medical retrieval basket with legs shaped to enhance capture and reduce trauma |
US6461370B1 (en) | 1998-11-03 | 2002-10-08 | C. R. Bard, Inc. | Temporary vascular filter guide wire |
US7491216B2 (en) | 1997-11-07 | 2009-02-17 | Salviac Limited | Filter element with retractable guidewire tip |
EP1028670B1 (en) | 1997-11-07 | 2008-01-02 | Salviac Limited | An embolic protection device |
US20040260333A1 (en) | 1997-11-12 | 2004-12-23 | Dubrul William R. | Medical device and method |
EP1030603B1 (en) | 1997-11-12 | 2008-08-13 | Genesis Technologies LLC. | Biological passageway occlusion removal |
US6443972B1 (en) | 1997-11-19 | 2002-09-03 | Cordis Europa N.V. | Vascular filter |
US6136015A (en) | 1998-08-25 | 2000-10-24 | Micrus Corporation | Vasoocclusive coil |
US6695864B2 (en) | 1997-12-15 | 2004-02-24 | Cardeon Corporation | Method and apparatus for cerebral embolic protection |
JP2002502626A (en) | 1998-02-10 | 2002-01-29 | アーテミス・メディカル・インコーポレイテッド | Supplementary device and method of using the same |
WO1999039649A1 (en) | 1998-02-10 | 1999-08-12 | Dubrul William R | Occlusion, anchoring, tensioning and flow direction apparatus and methods for use |
US5931866A (en) * | 1998-02-24 | 1999-08-03 | Frantzen; John J. | Radially expandable stent featuring accordion stops |
US20050131453A1 (en) | 1998-03-13 | 2005-06-16 | Parodi Juan C. | Apparatus and methods for reducing embolization during treatment of carotid artery disease |
US6423032B2 (en) | 1998-03-13 | 2002-07-23 | Arteria Medical Science, Inc. | Apparatus and methods for reducing embolization during treatment of carotid artery disease |
US6206868B1 (en) | 1998-03-13 | 2001-03-27 | Arteria Medical Science, Inc. | Protective device and method against embolization during treatment of carotid artery disease |
DE69933657T2 (en) | 1998-04-02 | 2007-08-23 | Salviac Ltd. | IMPLANTATION CATHETER |
IE980241A1 (en) | 1998-04-02 | 1999-10-20 | Salviac Ltd | Delivery catheter with split sheath |
US5944728A (en) | 1998-04-23 | 1999-08-31 | Boston Scientific Corporation | Surgical retrieval basket with the ability to capture and release material |
US6450989B2 (en) | 1998-04-27 | 2002-09-17 | Artemis Medical, Inc. | Dilating and support apparatus with disease inhibitors and methods for use |
US6007557A (en) | 1998-04-29 | 1999-12-28 | Embol-X, Inc. | Adjustable blood filtration system |
US6511492B1 (en) | 1998-05-01 | 2003-01-28 | Microvention, Inc. | Embolectomy catheters and methods for treating stroke and other small vessel thromboembolic disorders |
US6908474B2 (en) | 1998-05-13 | 2005-06-21 | Gore Enterprise Holdings, Inc. | Apparatus and methods for reducing embolization during treatment of carotid artery disease |
EP1082072B8 (en) | 1998-06-04 | 2014-03-05 | New York University | Endovascular thin film devices for treating and preventing stroke |
IL124958A0 (en) | 1998-06-16 | 1999-01-26 | Yodfat Ofer | Implantable blood filtering device |
US6241746B1 (en) | 1998-06-29 | 2001-06-05 | Cordis Corporation | Vascular filter convertible to a stent and method |
NL1009551C2 (en) | 1998-07-03 | 2000-01-07 | Cordis Europ | Vena cava filter with improvements for controlled ejection. |
US6261319B1 (en) * | 1998-07-08 | 2001-07-17 | Scimed Life Systems, Inc. | Stent |
US6306163B1 (en) | 1998-08-04 | 2001-10-23 | Advanced Cardiovascular Systems, Inc. | Assembly for collecting emboli and method of use |
US6231588B1 (en) | 1998-08-04 | 2001-05-15 | Percusurge, Inc. | Low profile catheter for angioplasty and occlusion |
US6179860B1 (en) | 1998-08-19 | 2001-01-30 | Artemis Medical, Inc. | Target tissue localization device and method |
US6328755B1 (en) | 1998-09-24 | 2001-12-11 | Scimed Life Systems, Inc. | Filter delivery device |
US6051014A (en) | 1998-10-13 | 2000-04-18 | Embol-X, Inc. | Percutaneous filtration catheter for valve repair surgery and methods of use |
US6042597A (en) * | 1998-10-23 | 2000-03-28 | Scimed Life Systems, Inc. | Helical stent design |
US7128073B1 (en) | 1998-11-06 | 2006-10-31 | Ev3 Endovascular, Inc. | Method and device for left atrial appendage occlusion |
US7044134B2 (en) | 1999-11-08 | 2006-05-16 | Ev3 Sunnyvale, Inc | Method of implanting a device in the left atrial appendage |
US6083259A (en) * | 1998-11-16 | 2000-07-04 | Frantzen; John J. | Axially non-contracting flexible radially expandable stent |
US6083239A (en) | 1998-11-24 | 2000-07-04 | Embol-X, Inc. | Compliant framework and methods of use |
US6102932A (en) | 1998-12-15 | 2000-08-15 | Micrus Corporation | Intravascular device push wire delivery system |
US6652554B1 (en) | 1999-01-04 | 2003-11-25 | Mark H. Wholey | Instrument for thromboembolic protection |
US6254609B1 (en) | 1999-01-11 | 2001-07-03 | Scimed Life Systems, Inc. | Self-expanding stent delivery system with two sheaths |
US6896690B1 (en) | 2000-01-27 | 2005-05-24 | Viacor, Inc. | Cardiac valve procedure methods and devices |
DE60042316D1 (en) | 1999-01-28 | 2009-07-16 | Salviac Ltd | CATHETER WITH EXPANDABLE END CUT |
US7018401B1 (en) | 1999-02-01 | 2006-03-28 | Board Of Regents, The University Of Texas System | Woven intravascular devices and methods for making the same and apparatus for delivery of the same |
US6991641B2 (en) | 1999-02-12 | 2006-01-31 | Cordis Corporation | Low profile vascular filter system |
US20020138094A1 (en) | 1999-02-12 | 2002-09-26 | Thomas Borillo | Vascular filter system |
US6171327B1 (en) | 1999-02-24 | 2001-01-09 | Scimed Life Systems, Inc. | Intravascular filter and method |
US6355051B1 (en) | 1999-03-04 | 2002-03-12 | Bioguide Consulting, Inc. | Guidewire filter device |
US20020169474A1 (en) | 1999-03-08 | 2002-11-14 | Microvena Corporation | Minimally invasive medical device deployment and retrieval system |
US6632236B2 (en) | 1999-03-12 | 2003-10-14 | Arteria Medical Science, Inc. | Catheter having radially expandable main body |
US6245012B1 (en) | 1999-03-19 | 2001-06-12 | Nmt Medical, Inc. | Free standing filter |
US6893450B2 (en) | 1999-03-26 | 2005-05-17 | Cook Urological Incorporated | Minimally-invasive medical retrieval device |
US6277139B1 (en) | 1999-04-01 | 2001-08-21 | Scion Cardio-Vascular, Inc. | Vascular protection and embolic material retriever |
US6743247B1 (en) | 1999-04-01 | 2004-06-01 | Scion Cardio-Vascular, Inc. | Locking frame, filter and deployment system |
US6277138B1 (en) | 1999-08-17 | 2001-08-21 | Scion Cardio-Vascular, Inc. | Filter for embolic material mounted on expandable frame |
US6537296B2 (en) | 1999-04-01 | 2003-03-25 | Scion Cardio-Vascular, Inc. | Locking frame, filter and deployment system |
US7150756B2 (en) | 1999-04-01 | 2006-12-19 | Scion Cardio-Vascular, Inc | Radiopaque locking frame, filter and flexible end |
US6340465B1 (en) | 1999-04-12 | 2002-01-22 | Edwards Lifesciences Corp. | Lubricious coatings for medical devices |
US6267776B1 (en) | 1999-05-03 | 2001-07-31 | O'connell Paul T. | Vena cava filter and method for treating pulmonary embolism |
DE20080298U1 (en) | 1999-05-07 | 2001-12-20 | Salviac Ltd | Embolic protection device |
US7014647B2 (en) | 1999-05-07 | 2006-03-21 | Salviac Limited | Support frame for an embolic protection device |
WO2000067665A1 (en) | 1999-05-07 | 2000-11-16 | Salviac Limited | Support frame for embolic protection device |
US20020058911A1 (en) | 1999-05-07 | 2002-05-16 | Paul Gilson | Support frame for an embolic protection device |
US6918921B2 (en) | 1999-05-07 | 2005-07-19 | Salviac Limited | Support frame for an embolic protection device |
WO2000067666A1 (en) | 1999-05-07 | 2000-11-16 | Salviac Limited | Improved filter element for embolic protection device |
US6964672B2 (en) | 1999-05-07 | 2005-11-15 | Salviac Limited | Support frame for an embolic protection device |
US6585756B1 (en) | 1999-05-14 | 2003-07-01 | Ernst P. Strecker | Implantable lumen prosthesis |
US6176849B1 (en) | 1999-05-21 | 2001-01-23 | Scimed Life Systems, Inc. | Hydrophilic lubricity coating for medical devices comprising a hydrophobic top coat |
FR2794653B1 (en) | 1999-06-14 | 2001-12-21 | Sarl Aln | KIT FOR THE REMOVAL OF A BLADDER VESSEL FILTER OF THE UMBRELLA TYPE |
US6458139B1 (en) | 1999-06-21 | 2002-10-01 | Endovascular Technologies, Inc. | Filter/emboli extractor for use in variable sized blood vessels |
US6179859B1 (en) | 1999-07-16 | 2001-01-30 | Baff Llc | Emboli filtration system and methods of use |
US6468291B2 (en) | 1999-07-16 | 2002-10-22 | Baff Llc | Emboli filtration system having integral strut arrangement and methods of use |
US20030150821A1 (en) | 1999-07-16 | 2003-08-14 | Bates Mark C. | Emboli filtration system and methods of use |
US6485507B1 (en) | 1999-07-28 | 2002-11-26 | Scimed Life Systems | Multi-property nitinol by heat treatment |
US7229463B2 (en) | 1999-07-30 | 2007-06-12 | Angioguard, Inc. | Vascular filter system for cardiopulmonary bypass |
US7320697B2 (en) | 1999-07-30 | 2008-01-22 | Boston Scientific Scimed, Inc. | One piece loop and coil |
US6589263B1 (en) | 1999-07-30 | 2003-07-08 | Incept Llc | Vascular device having one or more articulation regions and methods of use |
US6620182B1 (en) | 1999-07-30 | 2003-09-16 | Incept Llc | Vascular filter having articulation region and methods of use in the ascending aorta |
US6179861B1 (en) | 1999-07-30 | 2001-01-30 | Incept Llc | Vascular device having one or more articulation regions and methods of use |
US6214026B1 (en) | 1999-07-30 | 2001-04-10 | Incept Llc | Delivery system for a vascular device with articulation region |
US6371970B1 (en) | 1999-07-30 | 2002-04-16 | Incept Llc | Vascular filter having articulation region and methods of use in the ascending aorta |
WO2001008742A1 (en) | 1999-07-30 | 2001-02-08 | Incept Llc | Vascular filter having articulation region and methods of use in the ascending aorta |
US7229462B2 (en) | 1999-07-30 | 2007-06-12 | Angioguard, Inc. | Vascular filter system for carotid endarterectomy |
US6544279B1 (en) | 2000-08-09 | 2003-04-08 | Incept, Llc | Vascular device for emboli, thrombus and foreign body removal and methods of use |
US6203561B1 (en) | 1999-07-30 | 2001-03-20 | Incept Llc | Integrated vascular device having thrombectomy element and vascular filter and methods of use |
US7306618B2 (en) | 1999-07-30 | 2007-12-11 | Incept Llc | Vascular device for emboli and thrombi removal and methods of use |
US6530939B1 (en) | 1999-07-30 | 2003-03-11 | Incept, Llc | Vascular device having articulation region and methods of use |
US6616679B1 (en) | 1999-07-30 | 2003-09-09 | Incept, Llc | Rapid exchange vascular device for emboli and thrombus removal and methods of use |
US6142987A (en) | 1999-08-03 | 2000-11-07 | Scimed Life Systems, Inc. | Guided filter with support wire and methods of use |
US6245087B1 (en) | 1999-08-03 | 2001-06-12 | Embol-X, Inc. | Variable expansion frame system for deploying medical devices and methods of use |
US6346116B1 (en) | 1999-08-03 | 2002-02-12 | Medtronic Ave, Inc. | Distal protection device |
US6168579B1 (en) | 1999-08-04 | 2001-01-02 | Scimed Life Systems, Inc. | Filter flush system and methods of use |
US6235044B1 (en) | 1999-08-04 | 2001-05-22 | Scimed Life Systems, Inc. | Percutaneous catheter and guidewire for filtering during ablation of mycardial or vascular tissue |
US6273901B1 (en) | 1999-08-10 | 2001-08-14 | Scimed Life Systems, Inc. | Thrombosis filter having a surface treatment |
EP1402848B2 (en) | 1999-08-27 | 2018-10-24 | Covidien LP | Slideable vascular filter |
US6251122B1 (en) | 1999-09-02 | 2001-06-26 | Scimed Life Systems, Inc. | Intravascular filter retrieval device and method |
US6187025B1 (en) | 1999-09-09 | 2001-02-13 | Noble-Met, Ltd. | Vascular filter |
DE29916162U1 (en) | 1999-09-14 | 2000-01-13 | Cormedics Gmbh | Vascular filter system |
US6325815B1 (en) | 1999-09-21 | 2001-12-04 | Microvena Corporation | Temporary vascular filter |
US6939361B1 (en) | 1999-09-22 | 2005-09-06 | Nmt Medical, Inc. | Guidewire for a free standing intervascular device having an integral stop mechanism |
US6375670B1 (en) | 1999-10-07 | 2002-04-23 | Prodesco, Inc. | Intraluminal filter |
US6364895B1 (en) | 1999-10-07 | 2002-04-02 | Prodesco, Inc. | Intraluminal filter |
US6331189B1 (en) * | 1999-10-18 | 2001-12-18 | Medtronic, Inc. | Flexible medical stent |
US6340364B2 (en) | 1999-10-22 | 2002-01-22 | Nozomu Kanesaka | Vascular filtering device |
US6264672B1 (en) | 1999-10-25 | 2001-07-24 | Biopsy Sciences, Llc | Emboli capturing device |
US6425909B1 (en) | 1999-11-04 | 2002-07-30 | Concentric Medical, Inc. | Methods and devices for filtering fluid flow through a body structure |
US6171328B1 (en) | 1999-11-09 | 2001-01-09 | Embol-X, Inc. | Intravascular catheter filter with interlocking petal design and methods of use |
US6371971B1 (en) | 1999-11-15 | 2002-04-16 | Scimed Life Systems, Inc. | Guidewire filter and methods of use |
AU1623201A (en) | 1999-11-18 | 2001-05-30 | Advanced Cardiovascular Systems Inc. | Embolic protection system and method including an emboli-capturing catheter |
US6331184B1 (en) | 1999-12-10 | 2001-12-18 | Scimed Life Systems, Inc. | Detachable covering for an implantable medical device |
US6623450B1 (en) | 1999-12-17 | 2003-09-23 | Advanced Cardiovascular Systems, Inc. | System for blocking the passage of emboli through a body vessel |
US6443979B1 (en) | 1999-12-20 | 2002-09-03 | Advanced Cardiovascular Systems, Inc. | Expandable stent delivery sheath and method of use |
US6443971B1 (en) | 1999-12-21 | 2002-09-03 | Advanced Cardiovascular Systems, Inc. | System for, and method of, blocking the passage of emboli through a vessel |
US6575997B1 (en) | 1999-12-23 | 2003-06-10 | Endovascular Technologies, Inc. | Embolic basket |
US6402771B1 (en) | 1999-12-23 | 2002-06-11 | Guidant Endovascular Solutions | Snare |
US6660021B1 (en) | 1999-12-23 | 2003-12-09 | Advanced Cardiovascular Systems, Inc. | Intravascular device and system |
US6406471B1 (en) | 1999-12-28 | 2002-06-18 | Embol-X, Inc. | Arterial filter with aspiration and methods of use |
US6290710B1 (en) | 1999-12-29 | 2001-09-18 | Advanced Cardiovascular Systems, Inc. | Embolic protection device |
US6540722B1 (en) | 1999-12-30 | 2003-04-01 | Advanced Cardiovascular Systems, Inc. | Embolic protection devices |
US6645220B1 (en) | 1999-12-30 | 2003-11-11 | Advanced Cardiovascular Systems, Inc. | Embolic protection system and method including and embolic-capturing filter |
US6702834B1 (en) | 1999-12-30 | 2004-03-09 | Advanced Cardiovascular Systems, Inc. | Embolic protection devices |
US6290656B1 (en) | 1999-12-30 | 2001-09-18 | Advanced Cardiovascular Systems, Inc. | Guide wire with damped force vibration mechanism |
US6695813B1 (en) | 1999-12-30 | 2004-02-24 | Advanced Cardiovascular Systems, Inc. | Embolic protection devices |
US6383206B1 (en) | 1999-12-30 | 2002-05-07 | Advanced Cardiovascular Systems, Inc. | Embolic protection system and method including filtering elements |
US6511503B1 (en) | 1999-12-30 | 2003-01-28 | Advanced Cardiovascular Systems, Inc. | Catheter apparatus for treating occluded vessels and filtering embolic debris and method of use |
US6361546B1 (en) | 2000-01-13 | 2002-03-26 | Endotex Interventional Systems, Inc. | Deployable recoverable vascular filter and methods for use |
US6692513B2 (en) | 2000-06-30 | 2004-02-17 | Viacor, Inc. | Intravascular filter with debris entrapment mechanism |
US6443926B1 (en) | 2000-02-01 | 2002-09-03 | Harold D. Kletschka | Embolic protection device having expandable trap |
DE60128207T2 (en) | 2000-02-01 | 2008-01-10 | Harold D. Minneapolis Kletschka | ANGIOPLASTIEVORRICHTUNNG |
US6517550B1 (en) | 2000-02-02 | 2003-02-11 | Board Of Regents, The University Of Texas System | Foreign body retrieval device |
US6540767B1 (en) | 2000-02-08 | 2003-04-01 | Scimed Life Systems, Inc. | Recoilable thrombosis filtering device and method |
US6540768B1 (en) | 2000-02-09 | 2003-04-01 | Cordis Corporation | Vascular filter system |
US6863696B2 (en) | 2000-02-16 | 2005-03-08 | Viktoria Kantsevitcha | Vascular prosthesis |
US6629953B1 (en) | 2000-02-18 | 2003-10-07 | Fox Hollow Technologies, Inc. | Methods and devices for removing material from a vascular site |
AU2001241603A1 (en) | 2000-02-23 | 2001-09-03 | Boston Scientific Limited | Intravascular filtering devices and methods |
ATE353604T1 (en) | 2000-03-10 | 2007-03-15 | Michael Anthony T Don | FILTER EXPANSION DEVICE FOR PREVENTING VASCULAR EMBOLY |
US6695865B2 (en) | 2000-03-20 | 2004-02-24 | Advanced Bio Prosthetic Surfaces, Ltd. | Embolic protection device |
US6485500B1 (en) | 2000-03-21 | 2002-11-26 | Advanced Cardiovascular Systems, Inc. | Emboli protection system |
US6632241B1 (en) | 2000-03-22 | 2003-10-14 | Endovascular Technologies, Inc. | Self-expanding, pseudo-braided intravascular device |
US6514273B1 (en) | 2000-03-22 | 2003-02-04 | Endovascular Technologies, Inc. | Device for removal of thrombus through physiological adhesion |
US20040167567A1 (en) | 2001-03-23 | 2004-08-26 | Cano Gerald G. | Method and apparatus for capturing objects beyond an operative site in medical procedures |
GB2369575A (en) | 2000-04-20 | 2002-06-05 | Salviac Ltd | An embolic protection system |
US6706053B1 (en) | 2000-04-28 | 2004-03-16 | Advanced Cardiovascular Systems, Inc. | Nitinol alloy design for sheath deployable and re-sheathable vascular devices |
US6592616B1 (en) | 2000-04-28 | 2003-07-15 | Advanced Cardiovascular Systems, Inc. | System and device for minimizing embolic risk during an interventional procedure |
US6520978B1 (en) | 2000-05-15 | 2003-02-18 | Intratherapeutics, Inc. | Emboli filter |
US6602271B2 (en) | 2000-05-24 | 2003-08-05 | Medtronic Ave, Inc. | Collapsible blood filter with optimal braid geometry |
US6645221B1 (en) | 2000-05-30 | 2003-11-11 | Zuli, Holdings Ltd. | Active arterial embolization filter |
US6939362B2 (en) | 2001-11-27 | 2005-09-06 | Advanced Cardiovascular Systems, Inc. | Offset proximal cage for embolic filtering devices |
US6565591B2 (en) | 2000-06-23 | 2003-05-20 | Salviac Limited | Medical device |
US6663650B2 (en) | 2000-06-29 | 2003-12-16 | Concentric Medical, Inc. | Systems, methods and devices for removing obstructions from a blood vessel |
US8298257B2 (en) | 2000-06-29 | 2012-10-30 | Concentric Medical, Inc. | Systems, methods and devices for removing obstructions from a blood vessel |
US6482222B1 (en) | 2000-07-11 | 2002-11-19 | Rafael Medical Technologies Inc. | Intravascular filter |
US6964670B1 (en) | 2000-07-13 | 2005-11-15 | Advanced Cardiovascular Systems, Inc. | Embolic protection guide wire |
US6575995B1 (en) | 2000-07-14 | 2003-06-10 | Advanced Cardiovascular Systems, Inc. | Expandable cage embolic material filter system and method |
US6656202B2 (en) | 2000-07-14 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Embolic protection systems |
US6679902B1 (en) | 2000-07-19 | 2004-01-20 | Advanced Cardiovascular Systems, Inc. | Reduced profile delivery sheath for use in interventional procedures |
US6740061B1 (en) | 2000-07-28 | 2004-05-25 | Ev3 Inc. | Distal protection device |
US6527746B1 (en) | 2000-08-03 | 2003-03-04 | Ev3, Inc. | Back-loading catheter |
US7147649B2 (en) | 2000-08-04 | 2006-12-12 | Duke University | Temporary vascular filters |
US6394978B1 (en) | 2000-08-09 | 2002-05-28 | Advanced Cardiovascular Systems, Inc. | Interventional procedure expandable balloon expansion enabling system and method |
US6485501B1 (en) | 2000-08-11 | 2002-11-26 | Cordis Corporation | Vascular filter system with guidewire and capture mechanism |
JP2004506469A (en) | 2000-08-18 | 2004-03-04 | アトリテック, インコーポレイテッド | Expandable implantable device for filtering blood flow from the atrial appendage |
US6558405B1 (en) | 2000-08-29 | 2003-05-06 | Advanced Cardiovascular Systems, Inc. | Embolic filter |
FR2813518B1 (en) | 2000-09-04 | 2002-10-31 | Claude Mialhe | VASCULAR OCCLUSION DEVICE, APPARATUS AND METHOD OF USE |
US6511496B1 (en) | 2000-09-12 | 2003-01-28 | Advanced Cardiovascular Systems, Inc. | Embolic protection device for use in interventional procedures |
US6723108B1 (en) | 2000-09-18 | 2004-04-20 | Cordis Neurovascular, Inc | Foam matrix embolization device |
US20020111590A1 (en) * | 2000-09-29 | 2002-08-15 | Davila Luis A. | Medical devices, drug coatings and methods for maintaining the drug coatings thereon |
US6616681B2 (en) | 2000-10-05 | 2003-09-09 | Scimed Life Systems, Inc. | Filter delivery and retrieval device |
US6537294B1 (en) | 2000-10-17 | 2003-03-25 | Advanced Cardiovascular Systems, Inc. | Delivery systems for embolic filter devices |
JP2004517652A (en) | 2000-10-18 | 2004-06-17 | エヌエムティー メディカル インコーポレイテッド | Interlock installation / separation mechanism over wire |
US6582447B1 (en) | 2000-10-20 | 2003-06-24 | Angiodynamics, Inc. | Convertible blood clot filter |
US6589265B1 (en) | 2000-10-31 | 2003-07-08 | Endovascular Technologies, Inc. | Intrasaccular embolic device |
US6616680B1 (en) | 2000-11-01 | 2003-09-09 | Joseph M. Thielen | Distal protection and delivery system and method |
US6602272B2 (en) | 2000-11-02 | 2003-08-05 | Advanced Cardiovascular Systems, Inc. | Devices configured from heat shaped, strain hardened nickel-titanium |
US6893451B2 (en) | 2000-11-09 | 2005-05-17 | Advanced Cardiovascular Systems, Inc. | Apparatus for capturing objects beyond an operative site utilizing a capture device delivered on a medical guide wire |
US6726703B2 (en) | 2000-11-27 | 2004-04-27 | Scimed Life Systems, Inc. | Distal protection device and method |
US6506203B1 (en) | 2000-12-19 | 2003-01-14 | Advanced Cardiovascular Systems, Inc. | Low profile sheathless embolic protection system |
US6582448B1 (en) | 2000-12-21 | 2003-06-24 | Advanced Cardiovascular Systems, Inc. | Vessel occlusion device for embolic protection system |
US6936059B2 (en) | 2001-01-16 | 2005-08-30 | Scimed Life Systems, Inc. | Endovascular guidewire filter and methods of use |
US7169165B2 (en) | 2001-01-16 | 2007-01-30 | Boston Scientific Scimed, Inc. | Rapid exchange sheath for deployment of medical devices and methods of use |
US6663651B2 (en) | 2001-01-16 | 2003-12-16 | Incept Llc | Systems and methods for vascular filter retrieval |
US6610077B1 (en) | 2001-01-23 | 2003-08-26 | Endovascular Technologies, Inc. | Expandable emboli filter and thrombectomy device |
US6689151B2 (en) | 2001-01-25 | 2004-02-10 | Scimed Life Systems, Inc. | Variable wall thickness for delivery sheath housing |
US20020128680A1 (en) | 2001-01-25 | 2002-09-12 | Pavlovic Jennifer L. | Distal protection device with electrospun polymer fiber matrix |
US6901287B2 (en) | 2001-02-09 | 2005-05-31 | Medtronic, Inc. | Implantable therapy delivery element adjustable anchor |
US6979343B2 (en) | 2001-02-14 | 2005-12-27 | Ev3 Inc. | Rolled tip recovery catheter |
US6506205B2 (en) | 2001-02-20 | 2003-01-14 | Mark Goldberg | Blood clot filtering system |
US6840950B2 (en) | 2001-02-20 | 2005-01-11 | Scimed Life Systems, Inc. | Low profile emboli capture device |
US6569184B2 (en) | 2001-02-27 | 2003-05-27 | Advanced Cardiovascular Systems, Inc. | Recovery system for retrieving an embolic protection device |
US6974468B2 (en) | 2001-02-28 | 2005-12-13 | Scimed Life Systems, Inc. | Filter retrieval catheter |
US7226464B2 (en) | 2001-03-01 | 2007-06-05 | Scimed Life Systems, Inc. | Intravascular filter retrieval device having an actuatable dilator tip |
US20020123755A1 (en) | 2001-03-01 | 2002-09-05 | Scimed Life Systems, Inc. | Embolic protection filter delivery sheath |
US6562058B2 (en) | 2001-03-02 | 2003-05-13 | Jacques Seguin | Intravascular filter system |
US6537295B2 (en) | 2001-03-06 | 2003-03-25 | Scimed Life Systems, Inc. | Wire and lock mechanism |
US20020128679A1 (en) | 2001-03-08 | 2002-09-12 | Embol-X, Inc. | Cerebral protection during carotid endarterectomy and methods of use |
CA2441119A1 (en) | 2001-03-08 | 2002-09-19 | Atritech, Inc. | Atrial filter implants |
US7214237B2 (en) | 2001-03-12 | 2007-05-08 | Don Michael T Anthony | Vascular filter with improved strength and flexibility |
US8298160B2 (en) | 2001-03-16 | 2012-10-30 | Ev3 Inc. | Wire convertible from over-the-wire length to rapid exchange length |
US6602269B2 (en) | 2001-03-30 | 2003-08-05 | Scimed Life Systems | Embolic devices capable of in-situ reinforcement |
US7101379B2 (en) | 2001-04-02 | 2006-09-05 | Acmi Corporation | Retrieval basket for a surgical device and system and method for manufacturing same |
US7044958B2 (en) | 2001-04-03 | 2006-05-16 | Medtronic Vascular, Inc. | Temporary device for capturing embolic material |
US6706055B2 (en) | 2001-04-03 | 2004-03-16 | Medtronic Ave Inc. | Guidewire apparatus for temporary distal embolic protection |
US20020161395A1 (en) | 2001-04-03 | 2002-10-31 | Nareak Douk | Guide wire apparatus for prevention of distal atheroembolization |
US6866677B2 (en) | 2001-04-03 | 2005-03-15 | Medtronic Ave, Inc. | Temporary intraluminal filter guidewire and methods of use |
US6911036B2 (en) | 2001-04-03 | 2005-06-28 | Medtronic Vascular, Inc. | Guidewire apparatus for temporary distal embolic protection |
US6428559B1 (en) | 2001-04-03 | 2002-08-06 | Cordis Corporation | Removable, variable-diameter vascular filter system |
US6818006B2 (en) | 2001-04-03 | 2004-11-16 | Medtronic Vascular, Inc. | Temporary intraluminal filter guidewire |
EP1379307B1 (en) | 2001-04-17 | 2006-03-22 | Salviac Limited | A catheter |
US6436121B1 (en) | 2001-04-30 | 2002-08-20 | Paul H. Blom | Removable blood filter |
US6746469B2 (en) | 2001-04-30 | 2004-06-08 | Advanced Cardiovascular Systems, Inc. | Balloon actuated apparatus having multiple embolic filters, and method of use |
US6645223B2 (en) | 2001-04-30 | 2003-11-11 | Advanced Cardiovascular Systems, Inc. | Deployment and recovery control systems for embolic protection devices |
US6814739B2 (en) | 2001-05-18 | 2004-11-09 | U.S. Endoscopy Group, Inc. | Retrieval device |
US6635070B2 (en) | 2001-05-21 | 2003-10-21 | Bacchus Vascular, Inc. | Apparatus and methods for capturing particulate material within blood vessels |
US6929652B1 (en) | 2001-06-01 | 2005-08-16 | Advanced Cardiovascular Systems, Inc. | Delivery and recovery systems having steerability and rapid exchange operating modes for embolic protection systems |
US20020188314A1 (en) | 2001-06-07 | 2002-12-12 | Microvena Corporation | Radiopaque distal embolic protection device |
US6596011B2 (en) | 2001-06-12 | 2003-07-22 | Cordis Corporation | Emboli extraction catheter and vascular filter system |
US6551341B2 (en) | 2001-06-14 | 2003-04-22 | Advanced Cardiovascular Systems, Inc. | Devices configured from strain hardened Ni Ti tubing |
US6783538B2 (en) | 2001-06-18 | 2004-08-31 | Rex Medical, L.P | Removable vein filter |
US6793665B2 (en) | 2001-06-18 | 2004-09-21 | Rex Medical, L.P. | Multiple access vein filter |
US6623506B2 (en) | 2001-06-18 | 2003-09-23 | Rex Medical, L.P | Vein filter |
ATE372729T1 (en) | 2001-06-28 | 2007-09-15 | Lithotech Medical Ltd | DEVICE FOR CATCHING FOREIGN BODY |
US7678128B2 (en) | 2001-06-29 | 2010-03-16 | Advanced Cardiovascular Systems, Inc. | Delivery and recovery sheaths for medical devices |
US7338510B2 (en) | 2001-06-29 | 2008-03-04 | Advanced Cardiovascular Systems, Inc. | Variable thickness embolic filtering devices and method of manufacturing the same |
US6575996B1 (en) | 2001-06-29 | 2003-06-10 | Advanced Cardiovascular Systems, Inc. | Filter device for embolic protection system |
US6607554B2 (en) * | 2001-06-29 | 2003-08-19 | Advanced Cardiovascular Systems, Inc. | Universal stent link design |
US6599307B1 (en) | 2001-06-29 | 2003-07-29 | Advanced Cardiovascular Systems, Inc. | Filter device for embolic protection systems |
US6962598B2 (en) | 2001-07-02 | 2005-11-08 | Rubicon Medical, Inc. | Methods, systems, and devices for providing embolic protection |
US6997939B2 (en) | 2001-07-02 | 2006-02-14 | Rubicon Medical, Inc. | Methods, systems, and devices for deploying an embolic protection filter |
US6951570B2 (en) | 2001-07-02 | 2005-10-04 | Rubicon Medical, Inc. | Methods, systems, and devices for deploying a filter from a filter device |
US6878153B2 (en) | 2001-07-02 | 2005-04-12 | Rubicon Medical, Inc. | Methods, systems, and devices for providing embolic protection and removing embolic material |
JP4567918B2 (en) | 2001-07-02 | 2010-10-27 | テルモ株式会社 | Intravascular foreign matter removal wire and medical device |
EP1277448B1 (en) | 2001-07-13 | 2006-06-07 | B. Braun Medical SAS | System of vascular protection and angioplasty device |
US7011671B2 (en) | 2001-07-18 | 2006-03-14 | Atritech, Inc. | Cardiac implant device tether system and method |
US6656203B2 (en) | 2001-07-18 | 2003-12-02 | Cordis Corporation | Integral vascular filter system |
US6533800B1 (en) | 2001-07-25 | 2003-03-18 | Coaxia, Inc. | Devices and methods for preventing distal embolization using flow reversal in arteries having collateral blood flow |
US20030032941A1 (en) | 2001-08-13 | 2003-02-13 | Boyle William J. | Convertible delivery systems for medical devices |
US6902540B2 (en) | 2001-08-22 | 2005-06-07 | Gerald Dorros | Apparatus and methods for treating stroke and controlling cerebral flow characteristics |
US6551342B1 (en) | 2001-08-24 | 2003-04-22 | Endovascular Technologies, Inc. | Embolic filter |
US6652557B1 (en) | 2001-08-29 | 2003-11-25 | Macdonald Kenneth A. | Mechanism for capturing debris generated during vascular procedures |
US6638294B1 (en) | 2001-08-30 | 2003-10-28 | Advanced Cardiovascular Systems, Inc. | Self furling umbrella frame for carotid filter |
US6592606B2 (en) | 2001-08-31 | 2003-07-15 | Advanced Cardiovascular Systems, Inc. | Hinged short cage for an embolic protection device |
US6656351B2 (en) | 2001-08-31 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Embolic protection devices one way porous membrane |
US7097651B2 (en) | 2001-09-06 | 2006-08-29 | Advanced Cardiovascular Systems, Inc. | Embolic protection basket |
US6616682B2 (en) | 2001-09-19 | 2003-09-09 | Jomed Gmbh | Methods and apparatus for distal protection during a medical procedure |
US20030060843A1 (en) | 2001-09-27 | 2003-03-27 | Don Boucher | Vascular filter system with encapsulated filter |
US6878151B2 (en) | 2001-09-27 | 2005-04-12 | Scimed Life Systems, Inc. | Medical retrieval device |
US8262689B2 (en) | 2001-09-28 | 2012-09-11 | Advanced Cardiovascular Systems, Inc. | Embolic filtering devices |
US6755847B2 (en) | 2001-10-05 | 2004-06-29 | Scimed Life Systems, Inc. | Emboli capturing device and method of manufacture therefor |
US20030069597A1 (en) | 2001-10-10 | 2003-04-10 | Scimed Life Systems, Inc. | Loading tool |
US20030078614A1 (en) | 2001-10-18 | 2003-04-24 | Amr Salahieh | Vascular embolic filter devices and methods of use therefor |
US6887257B2 (en) | 2001-10-19 | 2005-05-03 | Incept Llc | Vascular embolic filter exchange devices and methods of use thereof |
US20030083692A1 (en) | 2001-10-29 | 2003-05-01 | Scimed Life Systems, Inc. | Distal protection device and method of use thereof |
US6790219B1 (en) | 2001-11-06 | 2004-09-14 | Edwards Lifesciences Corporation | Filter with integrated obturator tip and methods of use |
US20050021075A1 (en) | 2002-12-30 | 2005-01-27 | Bonnette Michael J. | Guidewire having deployable sheathless protective filter |
US20030109824A1 (en) | 2001-11-07 | 2003-06-12 | Microvena Corporation | Distal protection device with local drug delivery to maintain patency |
US6890340B2 (en) | 2001-11-29 | 2005-05-10 | Medtronic Vascular, Inc. | Apparatus for temporary intraluminal protection |
US6837898B2 (en) | 2001-11-30 | 2005-01-04 | Advanced Cardiovascular Systems, Inc. | Intraluminal delivery system for an attachable treatment device |
ES2399091T3 (en) | 2001-12-05 | 2013-03-25 | Keystone Heart Ltd. | Endovascular device for entrapment of particulate matter and method of use |
US7153320B2 (en) | 2001-12-13 | 2006-12-26 | Scimed Life Systems, Inc. | Hydraulic controlled retractable tip filter retrieval catheter |
US6748255B2 (en) | 2001-12-14 | 2004-06-08 | Biosense Webster, Inc. | Basket catheter with multiple location sensors |
US6741878B2 (en) | 2001-12-14 | 2004-05-25 | Biosense Webster, Inc. | Basket catheter with improved expansion mechanism |
US6793666B2 (en) | 2001-12-18 | 2004-09-21 | Scimed Life Systems, Inc. | Distal protection mechanically attached filter cartridge |
WO2003055413A2 (en) | 2001-12-21 | 2003-07-10 | Salviac Limited | A support frame for an embolic protection device |
US7241304B2 (en) | 2001-12-21 | 2007-07-10 | Advanced Cardiovascular Systems, Inc. | Flexible and conformable embolic filtering devices |
US6958074B2 (en) | 2002-01-07 | 2005-10-25 | Cordis Corporation | Releasable and retrievable vascular filter system |
US8647359B2 (en) | 2002-01-10 | 2014-02-11 | Boston Scientific Scimed, Inc. | Distal protection filter |
US6932830B2 (en) | 2002-01-10 | 2005-08-23 | Scimed Life Systems, Inc. | Disc shaped filter |
US20030135162A1 (en) | 2002-01-17 | 2003-07-17 | Scimed Life Systems, Inc. | Delivery and retrieval manifold for a distal protection filter |
JP4328209B2 (en) | 2002-01-25 | 2009-09-09 | アトリテック, インコーポレイテッド | Atrial appendage blood filtration system |
US20030144686A1 (en) | 2002-01-30 | 2003-07-31 | Embol-X, Inc. | Distal filtration devices and methods of use during aortic procedures |
US7344549B2 (en) | 2002-01-31 | 2008-03-18 | Advanced Cardiovascular Systems, Inc. | Expandable cages for embolic filtering devices |
US6953471B1 (en) | 2002-02-07 | 2005-10-11 | Edwards Lifesciences Corporation | Cannula with flexible remote cable filter deployment |
US6997938B2 (en) | 2002-02-12 | 2006-02-14 | Scimed Life Systems, Inc. | Embolic protection device |
US20030158574A1 (en) | 2002-02-15 | 2003-08-21 | Esch Brady D. | Flow-through aortic flow divider for cerebral and coronary embolic protection |
US7004964B2 (en) | 2002-02-22 | 2006-02-28 | Scimed Life Systems, Inc. | Apparatus and method for deployment of an endoluminal device |
EP1482861B1 (en) | 2002-03-05 | 2007-08-08 | Salviac Limited | An embolic protection system |
US6773448B2 (en) | 2002-03-08 | 2004-08-10 | Ev3 Inc. | Distal protection devices having controllable wire motion |
US7192434B2 (en) | 2002-03-08 | 2007-03-20 | Ev3 Inc. | Vascular protection devices and methods of use |
US20030176886A1 (en) | 2002-03-12 | 2003-09-18 | Wholey Mark H. | Vascular catheter with expanded distal tip for receiving a thromboembolic protection device and method of use |
US20030176884A1 (en) | 2002-03-12 | 2003-09-18 | Marwane Berrada | Everted filter device |
US7029440B2 (en) | 2002-03-13 | 2006-04-18 | Scimed Life Systems, Inc. | Distal protection filter and method of manufacture |
US6830844B2 (en) | 2002-03-27 | 2004-12-14 | Delphi Technologies, Inc. | Reversing air flow across a cathode for a fuel cell |
US20030187495A1 (en) | 2002-04-01 | 2003-10-02 | Cully Edward H. | Endoluminal devices, embolic filters, methods of manufacture and use |
US20030191493A1 (en) | 2002-04-05 | 2003-10-09 | Epstein Gordon H. | Device for clot retrieval and distal protection |
US7162303B2 (en) * | 2002-04-08 | 2007-01-09 | Ardian, Inc. | Renal nerve stimulation method and apparatus for treatment of patients |
US20030199819A1 (en) | 2002-04-17 | 2003-10-23 | Beck Robert C. | Filter wire system |
US20030204168A1 (en) | 2002-04-30 | 2003-10-30 | Gjalt Bosma | Coated vascular devices |
US7060082B2 (en) | 2002-05-06 | 2006-06-13 | Scimed Life Systems, Inc. | Perfusion guidewire in combination with a distal filter |
US8070769B2 (en) | 2002-05-06 | 2011-12-06 | Boston Scientific Scimed, Inc. | Inverted embolic protection filter |
WO2003094798A1 (en) * | 2002-05-08 | 2003-11-20 | Abbott Laboratories | Endoprosthesis having foot extensions |
DE60324787D1 (en) | 2002-05-10 | 2009-01-02 | Salviac Ltd | SYSTEM FOR FILTERING EMBOLI |
AU2003231886A1 (en) | 2002-05-13 | 2003-11-11 | Salviac Limited | Retrieval catheter for an embolic filter |
US7585309B2 (en) | 2002-05-16 | 2009-09-08 | Boston Scientific Scimed, Inc. | Aortic filter |
US7001406B2 (en) | 2002-05-23 | 2006-02-21 | Scimed Life Systems Inc. | Cartridge embolic protection filter and methods of use |
US7959584B2 (en) | 2002-05-29 | 2011-06-14 | Boston Scientific Scimed, Inc. | Dedicated distal protection guidewires |
US7326224B2 (en) | 2002-06-11 | 2008-02-05 | Boston Scientific Scimed, Inc. | Shaft and wire lock |
US7717934B2 (en) | 2002-06-14 | 2010-05-18 | Ev3 Inc. | Rapid exchange catheters usable with embolic protection devices |
US6887258B2 (en) | 2002-06-26 | 2005-05-03 | Advanced Cardiovascular Systems, Inc. | Embolic filtering devices for bifurcated vessels |
US7172614B2 (en) | 2002-06-27 | 2007-02-06 | Advanced Cardiovascular Systems, Inc. | Support structures for embolic filtering devices |
US6696666B2 (en) | 2002-07-03 | 2004-02-24 | Scimed Life Systems, Inc. | Tubular cutting process and system |
US6969402B2 (en) | 2002-07-26 | 2005-11-29 | Syntheon, Llc | Helical stent having flexible transition zone |
US7303575B2 (en) | 2002-08-01 | 2007-12-04 | Lumen Biomedical, Inc. | Embolism protection devices |
US6969395B2 (en) | 2002-08-07 | 2005-11-29 | Boston Scientific Scimed, Inc. | Electroactive polymer actuated medical devices |
US7115138B2 (en) | 2002-09-04 | 2006-10-03 | Boston Scientific Scimed, Inc. | Sheath tip |
US7174636B2 (en) | 2002-09-04 | 2007-02-13 | Scimed Life Systems, Inc. | Method of making an embolic filter |
US7056328B2 (en) | 2002-09-18 | 2006-06-06 | Arnott Richard J | Apparatus for capturing objects beyond an operative site utilizing a capture device delivered on a medical guide wire |
US7331973B2 (en) | 2002-09-30 | 2008-02-19 | Avdanced Cardiovascular Systems, Inc. | Guide wire with embolic filtering attachment |
US7252675B2 (en) | 2002-09-30 | 2007-08-07 | Advanced Cardiovascular, Inc. | Embolic filtering devices |
US20040093011A1 (en) | 2002-10-01 | 2004-05-13 | Scimed Life Systems, Inc. | Embolic protection device with lesion length assessment markers |
US7998163B2 (en) | 2002-10-03 | 2011-08-16 | Boston Scientific Scimed, Inc. | Expandable retrieval device |
US7223283B2 (en) * | 2002-10-09 | 2007-05-29 | Boston Scientific Scimed, Inc. | Stent with improved flexibility |
AU2003300038A1 (en) | 2002-10-11 | 2004-05-04 | Scimed Life Systems, Inc. | Embolic entrapment sheath |
US20040093012A1 (en) | 2002-10-17 | 2004-05-13 | Cully Edward H. | Embolic filter frame having looped support strut elements |
US7481823B2 (en) | 2002-10-25 | 2009-01-27 | Boston Scientific Scimed, Inc. | Multiple membrane embolic protection filter |
JP2006514846A (en) | 2002-10-29 | 2006-05-18 | サード ピーコック、ジェームス、シー. | Emboli filter device and related system and method |
US20040088000A1 (en) | 2002-10-31 | 2004-05-06 | Muller Paul F. | Single-wire expandable cages for embolic filtering devices |
US6989021B2 (en) | 2002-10-31 | 2006-01-24 | Cordis Corporation | Retrievable medical filter |
US20040098022A1 (en) | 2002-11-14 | 2004-05-20 | Barone David D. | Intraluminal catheter with hydraulically collapsible self-expanding protection device |
US20040111111A1 (en) | 2002-12-10 | 2004-06-10 | Scimed Life Systems, Inc. | Intravascular filter membrane with shape memory |
US7128752B2 (en) | 2002-12-23 | 2006-10-31 | Syntheon, Llc | Emboli and thrombi filter device and method of using the same |
US7625389B2 (en) | 2002-12-30 | 2009-12-01 | Boston Scientific Scimed, Inc. | Embolic protection device |
US20040138693A1 (en) | 2003-01-14 | 2004-07-15 | Scimed Life Systems, Inc. | Snare retrievable embolic protection filter with guidewire stopper |
US20040138694A1 (en) | 2003-01-15 | 2004-07-15 | Scimed Life Systems, Inc. | Intravascular filtering membrane and method of making an embolic protection filter device |
US7422595B2 (en) | 2003-01-17 | 2008-09-09 | Scion Cardio-Vascular, Inc. | Proximal actuator for medical device |
US20040147955A1 (en) | 2003-01-28 | 2004-07-29 | Scimed Life Systems, Inc. | Embolic protection filter having an improved filter frame |
US20040153119A1 (en) | 2003-01-30 | 2004-08-05 | Kusleika Richard S. | Embolic filters with a distal loop or no loop |
US7220271B2 (en) | 2003-01-30 | 2007-05-22 | Ev3 Inc. | Embolic filters having multiple layers and controlled pore size |
US7163549B2 (en) | 2003-02-11 | 2007-01-16 | Boston Scientific Scimed Inc. | Filter membrane manufacturing method |
JP2004261235A (en) | 2003-02-20 | 2004-09-24 | Kaneka Medix Corp | Medical wire device |
US7740644B2 (en) | 2003-02-24 | 2010-06-22 | Boston Scientific Scimed, Inc. | Embolic protection filtering device that can be adapted to be advanced over a guidewire |
US20040167566A1 (en) | 2003-02-24 | 2004-08-26 | Scimed Life Systems, Inc. | Apparatus for anchoring an intravascular device along a guidewire |
US7137991B2 (en) | 2003-02-24 | 2006-11-21 | Scimed Life Systems, Inc. | Multi-wire embolic protection filtering device |
US20040172055A1 (en) | 2003-02-27 | 2004-09-02 | Huter Scott J. | Embolic filtering devices |
US8591540B2 (en) | 2003-02-27 | 2013-11-26 | Abbott Cardiovascular Systems Inc. | Embolic filtering devices |
US7909862B2 (en) | 2003-03-19 | 2011-03-22 | Cook Medical Technologies Llc | Delivery systems and methods for deploying expandable intraluminal medical devices |
US6960370B2 (en) | 2003-03-27 | 2005-11-01 | Scimed Life Systems, Inc. | Methods of forming medical devices |
US20040193208A1 (en) | 2003-03-27 | 2004-09-30 | Scimed Life Systems, Inc. | Radiopaque embolic protection filter membrane |
EP1608295B1 (en) | 2003-03-28 | 2017-05-03 | Covidien LP | Double ended intravascular medical device |
US20040199199A1 (en) | 2003-04-02 | 2004-10-07 | Scimed Life Systems, Inc. | Filter and method of making a filter |
US6902572B2 (en) | 2003-04-02 | 2005-06-07 | Scimed Life Systems, Inc. | Anchoring mechanisms for intravascular devices |
US20040204737A1 (en) | 2003-04-11 | 2004-10-14 | Scimed Life Systems, Inc. | Embolic filter loop fabricated from composite material |
US7591832B2 (en) | 2003-04-24 | 2009-09-22 | Medtronic, Inc. | Expandable guide sheath and apparatus with distal protection and methods for use |
US7604649B2 (en) | 2003-04-29 | 2009-10-20 | Rex Medical, L.P. | Distal protection device |
US7331976B2 (en) | 2003-04-29 | 2008-02-19 | Rex Medical, L.P. | Distal protection device |
EP1472996B1 (en) | 2003-04-30 | 2009-09-30 | Medtronic Vascular, Inc. | Percutaneously delivered temporary valve |
US7942892B2 (en) | 2003-05-01 | 2011-05-17 | Abbott Cardiovascular Systems Inc. | Radiopaque nitinol embolic protection frame |
US6969396B2 (en) | 2003-05-07 | 2005-11-29 | Scimed Life Systems, Inc. | Filter membrane with increased surface area |
US20040249409A1 (en) | 2003-06-09 | 2004-12-09 | Scimed Life Systems, Inc. | Reinforced filter membrane |
US7537600B2 (en) | 2003-06-12 | 2009-05-26 | Boston Scientific Scimed, Inc. | Valved embolic protection filter |
US20050004594A1 (en) | 2003-07-02 | 2005-01-06 | Jeffrey Nool | Devices and methods for aspirating from filters |
US8337519B2 (en) | 2003-07-10 | 2012-12-25 | Boston Scientific Scimed, Inc. | Embolic protection filtering device |
US8535344B2 (en) | 2003-09-12 | 2013-09-17 | Rubicon Medical, Inc. | Methods, systems, and devices for providing embolic protection and removing embolic material |
US20050070953A1 (en) | 2003-09-18 | 2005-03-31 | Riley James W. | Medical device with flexible distal end loop and related methods of use |
US7604650B2 (en) | 2003-10-06 | 2009-10-20 | 3F Therapeutics, Inc. | Method and assembly for distal embolic protection |
US6994718B2 (en) | 2003-10-29 | 2006-02-07 | Medtronic Vascular, Inc. | Distal protection device for filtering and occlusion |
US8048103B2 (en) | 2003-11-06 | 2011-11-01 | Boston Scientific Scimed, Inc. | Flattened tip filter wire design |
US6972025B2 (en) | 2003-11-18 | 2005-12-06 | Scimed Life Systems, Inc. | Intravascular filter with bioabsorbable centering element |
US7354445B2 (en) | 2003-12-15 | 2008-04-08 | Medtronic Vascular Inc. | Embolic containment system with asymmetric frictional control |
US20050149110A1 (en) | 2003-12-16 | 2005-07-07 | Wholey Mark H. | Vascular catheter with an expandable section and a distal tip for delivering a thromboembolic protection device and method of use |
US20050159772A1 (en) | 2004-01-20 | 2005-07-21 | Scimed Life Systems, Inc. | Sheath for use with an embolic protection filtering device |
US20050159773A1 (en) | 2004-01-20 | 2005-07-21 | Scimed Life Systems, Inc. | Expandable retrieval device with dilator tip |
US8092483B2 (en) | 2004-03-06 | 2012-01-10 | Medtronic, Inc. | Steerable device having a corewire within a tube and combination with a functional medical component |
US7473265B2 (en) | 2004-03-15 | 2009-01-06 | Boston Scientific Scimed, Inc. | Filter media and methods of manufacture |
US7232462B2 (en) | 2004-03-31 | 2007-06-19 | Cook Incorporated | Self centering delivery catheter |
US8403976B2 (en) | 2004-04-08 | 2013-03-26 | Contego Medical Llc | Percutaneous transluminal angioplasty device with integral embolic filter |
US20050240215A1 (en) | 2004-04-21 | 2005-10-27 | Scimed Life Systems, Inc. | Magnetic embolic protection device and method |
US20050283148A1 (en) * | 2004-06-17 | 2005-12-22 | Janssen William M | Ablation apparatus and system to limit nerve conduction |
WO2006055052A2 (en) | 2004-07-19 | 2006-05-26 | Michael Gertner | Methods and devices for chronic embolic protection |
US20060020286A1 (en) | 2004-07-22 | 2006-01-26 | Volker Niermann | Device for filtering blood in a vessel with helical elements |
US20060020285A1 (en) | 2004-07-22 | 2006-01-26 | Volker Niermann | Method for filtering blood in a vessel with helical elements |
US7918872B2 (en) | 2004-07-30 | 2011-04-05 | Codman & Shurtleff, Inc. | Embolic device delivery system with retractable partially coiled-fiber release |
ATE520369T1 (en) | 2004-09-17 | 2011-09-15 | Nitinol Dev Corp | SHAPE MEMORY THIN FILM EMBOLIC PROTECTION DEVICE |
US8038696B2 (en) | 2004-12-06 | 2011-10-18 | Boston Scientific Scimed, Inc. | Sheath for use with an embolic protection filter |
US20060129181A1 (en) | 2004-12-13 | 2006-06-15 | Callol Joseph R | Retrieval device with retractable dilator tip |
US20060149313A1 (en) | 2004-12-30 | 2006-07-06 | Edward Arguello | Distal protection apparatus with improved wall apposition |
US20060149312A1 (en) | 2004-12-30 | 2006-07-06 | Edward Arguello | Distal protection device with improved wall apposition |
US7527637B2 (en) | 2005-01-07 | 2009-05-05 | Medtronic Vascular Inc. | Distal protection device for filtering and occlusion |
US20060206139A1 (en) | 2005-01-19 | 2006-09-14 | Tekulve Kurt J | Vascular occlusion device |
US20060184194A1 (en) | 2005-02-15 | 2006-08-17 | Cook Incorporated | Embolic protection device |
WO2006089178A2 (en) | 2005-02-18 | 2006-08-24 | Ev3 Inc. | Rapid exchange catheters and embolic protection devices |
US7867273B2 (en) * | 2007-06-27 | 2011-01-11 | Abbott Laboratories | Endoprostheses for peripheral arteries and other body vessels |
JP6522373B2 (en) | 2015-03-06 | 2019-05-29 | 愛三工業株式会社 | Evaporative fuel processing system |
-
2007
- 2007-06-27 US US11/769,410 patent/US7867273B2/en not_active Expired - Fee Related
-
2008
- 2008-05-16 WO PCT/US2008/063963 patent/WO2009002631A1/en active Application Filing
-
2010
- 2010-10-25 US US12/911,324 patent/US8382817B2/en active Active
Patent Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP1197189A2 (en) * | 2000-10-10 | 2002-04-17 | BIOTRONIK Mess- und Therapiegeräte GmbH & Co Ingenieurbüro Berlin | Stent |
Also Published As
Publication number | Publication date |
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US20110040370A1 (en) | 2011-02-17 |
US7867273B2 (en) | 2011-01-11 |
US20090005856A1 (en) | 2009-01-01 |
US8382817B2 (en) | 2013-02-26 |
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