US20050283222A1 - Apparatus for delivering endoluminal prostheses and methods of making and using them - Google Patents
Apparatus for delivering endoluminal prostheses and methods of making and using them Download PDFInfo
- Publication number
- US20050283222A1 US20050283222A1 US11/197,577 US19757705A US2005283222A1 US 20050283222 A1 US20050283222 A1 US 20050283222A1 US 19757705 A US19757705 A US 19757705A US 2005283222 A1 US2005283222 A1 US 2005283222A1
- Authority
- US
- United States
- Prior art keywords
- leaflets
- stent
- lumen
- sheath
- bumper
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Images
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
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/962—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve
- A61F2/966—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve with relative longitudinal movement between outer sleeve and prosthesis, e.g. using a push rod
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/962—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve
- A61F2/97—Instruments specially adapted for placement or removal of stents or stent-grafts having an outer sleeve the outer sleeve being splittable
Definitions
- the present invention relates generally to apparatus and methods for delivering endoluminal prostheses within body lumens of a patient, and more particularly to apparatus for delivering tubular prostheses or “stents” within a patient's vasculature for treating stenoses or other lesions, for example, within the coronary and carotid arteries, and to methods of making and using such apparatus.
- tubular prostheses or “stents” have been developed for maintaining the patency of a blood vessel, for example, following angioplasty or other procedures used to treat a stenosis, occlusion, or other lesion within the blood vessel.
- the stent may be implanted across a treatment site to scaffold the site and prevent it from subsequently contracting or otherwise becoming obstructed.
- the stent may be placed upon a catheter in a contracted condition, and the catheter advanced endoluminally to the treatment site until the stent is positioned across the stenosis.
- the stent may then be deployed and substantially anchored at the treatment site.
- the stent may be self-expanding, i.e., may be biased to expand to an enlarged condition upon release from the delivery catheter, thereby automatically substantially anchoring the stent at the treatment site.
- the stent may be plastically deformable, i.e., may be expanded with the aid of a balloon, which may underlie the stent on the catheter.
- the balloon may be inflated to expand the stent from the contracted condition to the enlarged condition wherein the stent substantially engages the wall of the treatment site.
- a balloon for example, on a separate balloon catheter, may also be used to further expand and/or anchor a self-expanding stent.
- a catheter including an array of electrodes, for example, on an expandable basket assembly may be provided.
- the device may be introduced into a body lumen, e.g., through the patient's vasculature into the heart, to treat conditions, such as heart arrhythmia.
- a sheath may be provided over the catheter to protect the elements on the distal end of the catheter, such as a stent, a balloon, and/or an array of electrodes.
- the sheath may be advanced distally over the proximal end of the catheter until it covers the distal end and the element(s) thereon, or the distal end of the catheter may be introduced into the sheath, and advanced until it is proximate the distal end of the sheath.
- the distal end of the catheter, with the overlying sheath thereon may then be introduced into a patient and positioned at a treatment site, whereupon the sheath may be retracted to expose the distal end of the catheter. After treatment, the sheath may be advanced back over the distal end of the catheter, and the entire device withdrawn from the patient.
- One of the problems associated with these devices is that they may have substantially blunt distal ends that may scrape along the wall of a vessel during advancement therethrough, possibly damaging the wall and/or dislodging embolic material from the wall.
- transition tips have been suggested for these devices.
- a conical or tapered nosepiece may be provided on the distal end of the catheter.
- a sheath may be disposed over the catheter, for example, to substantially cover the stent or other underlying element, such that the nosepiece extends distally from the end of the sheath, a distal edge of the sheath abutting the nosepiece.
- the nosepiece may facilitate advancement of the device through a narrow region of a blood vessel, although it may also risk catching on the wall of the vessel and/or dislodging embolic material, e.g., between the distal edge of the sheath and the nosepiece. Following delivery of a stent from the device, the nosepiece is generally positioned distal to the treated lesion.
- the proximal edge of the nosepiece may catch on the stent struts, resulting in the potential for trauma and embolic debris release.
- the sheath may be re-advanced across the treatment site to “recapture” the nosepiece, although in this approach the distal edge of the sheath may also catch on the stent struts.
- a sheath having a rounded distal end has been suggested, as disclosed in U.S. Pat. No. 5,593,412 issued to Martinez et al. Weakened areas or slits are provided in the distal end, thereby defining sections that may be softened upon introduction of warm saline solution. Once the sections are softened, the sheath may be retracted from an underlying balloon catheter to expose and implant a stent mounted on the catheter. Introduction of saline or other liquids into a patient's vasculature, however, may be undesirable, but is necessary in order to soften the sections on the distal end of the sheath and allow the stent to be deployed from the sheath.
- sheaths and/or catheters may buckle during insertion, because of the distal force applied from the proximal end to advance them through the patient's vasculature.
- they may kink when advanced through tortuous anatomy, possibly damaging the device or an element within the device.
- the present invention is directed to apparatus for delivering treatment elements, such as tubular prostheses or “stents,” within a body lumen of a patient, for example, for treating stenoses or other lesions within the coronary arteries, the carotid arteries, or other blood vessels, and to methods of making and using such apparatus.
- treatment elements such as tubular prostheses or “stents”
- an apparatus for delivering a prosthesis into a blood vessel of a patient that includes an elongate tubular member having a proximal end, a distal end, and a lumen extending between the proximal and distal ends.
- the distal end has a size for endoluminal insertion into a blood vessel and terminates in a substantially atraumatic distal portion including a plurality of flexible leaflets integrally molded thereto.
- the leaflets are deflectable from a closed position wherein the leaflets engage one another to an open position wherein the leaflets define an opening communicating with the lumen.
- the leaflets define a substantially rounded bullet shape in the closed position, although alternatively, the leaflets may define a substantially conical shape in the closed position.
- the leaflets are preferably substantially flexible and independently deflectable at a temperature less than body temperature, and are biased towards the closed position, but are resiliently deflectable to the open position. Adjacent leaflets may be separated by a slit, or may be connected to one another by weakened regions, the weakened regions being tearable upon retraction of the tubular member with respect to the prosthesis to allow the leaflets to be deflected towards the open position.
- a tubular prosthesis is disposed within the lumen proximate the distal portion.
- An elongate bumper member having a proximal end and a distal end is also provided, the bumper member being slidably disposed within the lumen of the sheath.
- the distal end of the bumper member has a blunt edge disposed adjacent to the proximal end of the prosthesis for preventing axial displacement of the prosthesis upon retraction of the tubular member with respect to the bumper member and/or the prosthesis.
- the prosthesis comprises a self-expanding stent, such as a coiled-sheet stent, the stent being biased to assume an expanded condition having a cross-section larger than the lumen of the tubular member, and being compressible to a contracted condition to facilitate insertion into the lumen.
- a self-expanding stent such as a coiled-sheet stent
- an apparatus for delivering a prosthesis into a blood vessel of a patient includes an elongate tubular member, such as that described above, having a proximal end, a distal end, and a lumen extending between the proximal and distal ends, the distal end having a size for endoluminal insertion into a blood vessel.
- a tubular prosthesis is disposed within the lumen proximate the distal end.
- An elongate bumper member is also provided that includes a helical coil having a proximal end and a distal end, the bumper member being slidably disposed within the lumen of the sheath. The distal end of the bumper member has a blunt distal edge disposed adjacent a proximal end of the prosthesis for preventing axial displacement of the prosthesis upon retraction of the tubular member with respect to the bumper member.
- the bumper member includes a helical wire compression coil, preferably a solid height coil, extending between its proximal and distal ends.
- a plastic bumper element extends from a distal end of the helical coil, the bumper element including the blunt distal edge thereon.
- An extension element extends distally from the bumper element, the extension element having a cross-section substantially smaller than the bumper element, whereby the extension element may extend through the prosthesis disposed within the lumen of the tubular member.
- the helical coil, bumper element, and/or the extension element include a lumen extending axially therethrough for receiving a guidewire therethrough.
- a method for making a sheath for delivering a treatment element within a body lumen of a patient is provided.
- a tubular member is provided that is formed from a substantially flexible material, the tubular member having a proximal end, a distal end, and a lumen extending axially between the proximal and distal ends, the distal end having a size for endoluminal insertion into a body lumen.
- a die is provided having a bore therein, the bore having a tapered shape. The die is heated to a temperature in excess of a melting point of the flexible material from which the tubular member is formed.
- the distal end of the tubular member is inserted into the bore of the heated die until a distal portion of the tubular member is softened and deformed into a tapered shape substantially enclosing the distal end.
- One or more slits are then created in the distal portion of the tubular member after it is deformed into the tapered shape, the slits defining a plurality of leaflets.
- a treatment element may be inserted into the lumen of the tubular member until it is disposed proximate the distal portion.
- a bullet having a tapered shape distal end is inserted into the distal end of the tubular member before inserting the distal end of the tubular member into the bore.
- the bullet and the bore have corresponding substantially rounded shapes defining a mold cavity therebetween when the distal end of the tubular member is inserted into the bore.
- the treatment element is a tubular prosthesis for implantation within a body lumen of a patient.
- the prosthesis is a self-expanding stent biased to assume an expanded condition having a cross-section larger than the lumen, and compressible to a contracted condition before being inserted into the lumen of the tubular member.
- the prosthesis may be inserted into the lumen of the tubular member before inserting the distal end of the tubular member into the bore, e.g., inserted into the lumen from the distal end of the tubular member.
- the prosthesis may be inserted into the lumen from the proximal end of the tubular member, e.g., either before or after the leaflets are formed on the distal portion of the tubular member.
- An elongate bumper member may be inserted into the lumen of the tubular member, the bumper member being slidably disposed within the lumen of the tubular member, the distal end having a blunt distal edge for abutting a proximal end of the prosthesis.
- an elongate helical coil may be provided having a proximal end and a distal end.
- a tubular bumper element may be attached to the distal end of the helical coil to provide the bumper member, the bumper element including the blunt distal edge of the bumper element.
- the bumper element is formed from plastic, and is attached to the helical coil by heating the bumper element until it is softened, and then directing the softened bumper element over the distal end of the helical coil.
- a tubular extension element may be attached to the bumper element, the extension element having a cross-section substantially smaller than the bumper element.
- FIG. 1A is a cross-sectional side view of a sheath having a rounded distal tip, in accordance with the present invention.
- FIG. 1B is a cross-sectional side view of an apparatus for delivering a stent, including the sheath of FIG. 1A .
- FIGS. 2A and 2B are end views of the sheath of FIGS. 1A and 1B , respectively.
- FIGS. 3A-3E are cross-sectional views showing a method for forming a rounded distal tip on a sheath, such as that shown in FIG. 1A .
- FIGS. 4A and 4B are cross-sectional views of a body lumen, showing a method for implanting a stent using an apparatus in accordance with the present invention.
- FIGS. 1A-2B show a preferred embodiment of an apparatus 10 for delivering a stent or other tubular prosthesis 50 into a blood vessel or other body lumen of a patient (not shown).
- the apparatus 10 includes an elongate tubular sheath 12 having a proximal end (not shown), a distal end 14 , and a lumen 16 extending generally therebetween.
- the tubular sheath 12 may be formed from a substantially flexible or semi-rigid material that may facilitate its advancement within a body lumen of a patient, preferably within the vasculature of a patient.
- the sheath 12 may be formed from a polymer, such as pebax, polyethylene, urethane, nylon, or other plastic material, that may be extruded or molded into elongate tubing of a desired length.
- the tubing has a wall thickness of between about 0.003-0.006 inch (0.075-0.150 mm), and has a substantially uniform outer diameter appropriate for the size of the stent being implanted, for example, between about 1.5-2.5 mm.
- the sheath 12 may have a substantially uniform construction along its length, or the sheath 12 may include portions along its length having varying degrees of flexibility.
- the sheath 12 includes a distal portion 18 formed entirely from a substantially flexible material, such as pebax, and an intermediate portion 20 formed from pebax including a stiffening element 22 therein.
- the intermediate portion 20 may include a braid or mesh, e.g., of stainless steel, laid over a teflon liner, with pebax tubing formed over the braid.
- the stiffening element 22 may be a helical wire coil and the like molded or otherwise formed in the tubing.
- the stiffening element 22 may enhance a rigidity of the intermediate portion 20 , for example, to reduce the risk of the intermediate portion 20 buckling or kinking, while still providing flexibility transverse to the longitudinal axis 28 , e.g., to accommodate advancement through tortuous anatomy.
- the sheath 12 also includes a proximal portion (not shown) that is formed from a more rigid material, such as nylon tubing, that may include a stiffening element as described above.
- the distal portion 18 has a length of between about 10-20 cm
- the intermediate portion 20 has a length of between about 20-30 cm
- the proximal portion has a length of between about 85-120 cm, more preferably about 100 cm or more.
- the distal portion 18 of the sheath 12 preferably has a rounded bullet shape defined by a plurality of flexible leaflets 24 that are integrally formed thereon.
- the leaflets 24 are preferably deflectable from a closed position, wherein adjacent leaflets 24 abut one another, to an open position. In the closed position, the leaflets 24 substantially close the lumen 16 , as shown in FIG. 2A .
- the leaflets 24 In the closed position, the leaflets 24 define a relatively small opening 25 where their apices meet.
- the leaflets 24 are spread apart to define an opening 26 communicating with the lumen 16 .
- the leaflets 24 are oriented substantially axially such that the opening 26 has a cross-section similar to the lumen 16 .
- the leaflets 24 are provided, although additional leaflets may be provided if desired.
- the leaflets 24 in the closed position, preferably define a substantially atraumatic distal portion 18 that may facilitate advancement of the sheath 12 endoluminally within a patient's vasculature with minimal risk of dislodging embolic material from and/or otherwise damaging the wall of a body lumen through which the sheath 12 is advanced.
- the leaflets 24 define a substantially rounded bullet shape in the closed position.
- leaflets 24 defining a substantially conical shape (not shown) in the closed position may be provided, with the leaflets 24 preferably biased to the closed position, as described below.
- the leaflets 24 are substantially flexible and independently deflectable substantially independent of the temperature to which the leaflets 24 are exposed, e.g., at a temperature substantially less than body temperature.
- the leaflets 24 are biased towards the closed position, but are resiliently deflectable to the open position. This may ensure that the opening 26 remains substantially closed until time of deployment of an element, such as stent 50 , from within the lumen 16 , and/or that the leaflets 24 do not catch on anything and open inadvertently. This may be particularly important when the apparatus 10 is advanced through tortuous anatomy, as described further below.
- the leaflets 24 may be at least partially plastically deformed when they are deflected from the closed position to the open position. In this alternative, the leaflets 24 may not return completely to the closed position when released from the fully open position, e.g., after the stent 50 is deployed from the apparatus 10 .
- adjacent leaflets 24 are separated by a relatively narrow slit 28 , although alternatively, the leaflets 24 may partially overlap with one another in the closed position.
- adjacent leaflets may be separated by a thin-walled or weakened region (not shown) that may be easily tearable upon retraction of the sheath 12 with respect to a stent or other element being deployed from within the lumen 16 . Once the weakened regions are torn, the leaflets may be freely deflected towards the open position as the element is being deployed.
- the leaflets 24 may have a thickness that is substantially thinner than a wall thickness of the rest of the distal portion 18 , preferably tapering towards their distal tips 24 a as shown in FIGS. 1A and 1B , thereby enhancing the flexibility of the leaflets 24 .
- the tapering thickness may also ensure that the leaflets 24 are biased towards the closed position, yet may deflect easily to accommodate a guidewire (not shown), bumper extension element, and the like, as described further below.
- the apparatus 10 also includes an elongate bumper member 30 that is slidably disposed within the sheath 12 .
- the bumper member 30 preferably includes a proximal end (not shown), a distal end 32 , and a lumen 34 that extends therebetween.
- the bumper member 30 preferably has a substantially uniform outer diameter slightly smaller than the interior lumen 16 of the sheath 12 , preferably by about 0.003-0.005 inch (0.075-0.125 mm) to create a close sliding, but not interfering, fit between the bumper member 30 and the sheath 12 .
- the lumen 34 has a diameter sufficiently large to accommodate a guidewire (not shown) therethrough, preferably between about 0.015-0.020 inch (0.375-0.500 mm), and more preferably about 0.016 inch (0.400 mm).
- the bumper member 30 is formed from a helical wire compression coil 36 , e.g., having adjacent turns that substantially abut one another.
- the coil 36 may be formed from flat or round wire, e.g., of stainless steel and the like, that is continuously helically wound along the length of the bumper member 30 , preferably a solid height coil.
- a relatively thin layer of teflon 38 and the like may be provided around the outside of the coil 36 to enhance a sliding relationship between the bumper member 30 and the sheath 12 . Because of the coil 36 , the bumper member 30 may be substantially resistant to buckling or kinking, while facilitating bending of the bumper member 30 transverse to the longitudinal axis 28 .
- a substantially rigid tubular segment may be attached to or otherwise extend from the proximal end of the coil 36 .
- the tubular segment is a section of hypotube having an inner lumen (not shown) similar to the lumen 34 of the coil 36 , and more preferably a two-stage length of hypotube that has a greater outer diameter on its proximal-most end.
- the tubular segment may facilitate distal advancement of the bumper member 30 into the sheath 12 with minimal risk of buckling and/or may provide enhanced tactile perception of relative movement of the bumper member 30 and the sheath 12 .
- a valve or other seal (not shown), e.g., for accommodating a guidewire therethrough while maintaining a fluid-tight seal, may also be provided on the proximal end of the tubular segment.
- the bumper member 30 also includes a tubular bumper element 40 on a distal end 37 of the coil 36 that includes a substantially blunt distal edge 42 .
- the bumper element 40 is preferably formed from pebax or other plastic material.
- a plastic bumper element 40 ensures no metal-to-metal contact, e.g., between the coil 36 of the bumper member 30 and the stent 50 that may lead to corrosion of the stent material.
- pebax and other substantially flexible materials may deform slightly, e.g., when the sheath 12 is retracted, to enhance contact between the blunt distal edge 42 of the bumper element 40 and the stent 50 .
- the bumper element 40 is preferably attached to the distal end 37 of the coil 36 , e.g., by heating the bumper element 40 to soften it and directing it over the distal end 37 , such that the bumper element is fused into the coils adjacent the distal end 37 .
- the bumper member 30 may also include a radiopaque or other marker 48 thereon for identifying a location of the bumper member 30 using external imaging, such as fluoroscopy.
- a platinum iridium ring 48 is provided on the bumper element 40 immediately adjacent the blunt distal edge 42 , thereby identifying a position of the proximal end 52 of the stent 50 .
- a marker (not shown) may be provided elsewhere on the apparatus 10 in addition to or instead of the marker 48 , such as on the sheath 12 or the stent 50 itself.
- the marker 48 may facilitate positioning of the apparatus 10 , and more particularly the stent 50 or other element therein, axially within a body lumen (not shown) before deploying the element from within the sheath 12 , as described further below.
- the bumper member 30 may also include a tubular extension element 44 that is thermally bonded or otherwise attached to and extends distally from the bumper element 40 .
- the extension element 44 has an outer diameter that is substantially smaller than the bumper element 40
- the extension element 44 may be partially inserted into the bumper element 40 as it is thermally bonded thereto so as not to interfere with the blunt edge 42 of the bumper element 40 .
- the extension element 44 has an outer diameter of about 0.66 mm (0.026 inch) to facilitate its insertion through the stent 50 , an inner diameter of about 0.41 mm (0.016 inch) to accommodate a guidewire therethrough, and a length of about 25 mm (1.0 inch).
- the extension element 44 may be appropriately sized larger or smaller to accommodate a guidewire, for example, between about 0.009-0.038 in (0.225-0.95 mm).
- the extension element 44 is preferably substantially flexible and has a substantially smooth outer surface to provide a low-friction, sliding contact with an element disposed within the sheath 12 .
- a stent 50 or other tubular prosthesis or graft may be disposed within the lumen 16 of the sheath 12 proximate the distal portion 18 .
- the stent 50 preferably is expandable between a contracted condition that facilitates its loading into the lumen 16 of the sheath 12 , and an enlarged condition for engaging a wall of a blood vessel or other body lumen (not shown).
- the stent 50 is a coiled-sheet stent, such as that disclosed in U.S. Pat. No. 5,443,400 issued to Sigwart, and/or in co-pending applications Ser. No. 09/347,845, filed Jul. 2, 1999, and Ser. No. 09/406,984, filed Sep.
- the stent 50 may be self-expanding, i.e., may be biased to assume the enlarged condition, but may be compressed and constrained in the contracted condition, for example, by the lumen 16 of the sheath 12 .
- the stent 50 may be plastically defonnable, i.e., may be substantially relaxed in the contracted condition, but may be forcibly expanded to the enlarged condition, for example, using a balloon catheter, as is known in the art.
- the apparatus 10 is provided pre-assembled with the stent 50 disposed within the lumen 16 of the sheath 12 adjacent the distal portion 18 of the sheath in its contracted condition.
- the bumper member 30 is also disposed within the lumen 16 such that the blunt edge 42 of the bumper element 40 is adjacent a proximal end 52 of the stent 50 .
- the extension element 44 preferably extends distally through the stent 50 and through the leaflets 24 , as best seen in FIGS. 1B and 2B .
- the extension element 44 may facilitate insertion of a guidewire (not shown) through the apparatus 10 , i.e., through the lumen 16 of the sheath 12 into the lumen 34 of the bumper member 30 to a proximal end of the apparatus 10 .
- a guidewire not shown
- the opening 25 at the apices of the leaflets 24 accommodates the extension element 44 therethrough without causing the leaflets 24 to partially buckle or bulge.
- the extension element 44 may be eliminated, and a guidewire inserted directly between the leaflets 24 into the lumens 16 , 34 .
- the apparatus 10 may be used to implant the stent 50 within a body lumen, preferably within a carotid artery, a coronary artery, a cerebral artery, a renal artery, or other blood vessel, as described further below.
- the apparatus 10 may incorporate “rapid exchange” configurations where a guidewire may exit from the lumens 16 , 34 of the sheath 12 and/or bumper member 30 through side ports (not shown) at a location along their lengths, i.e., at an intermediate location, rather than at their proximal ends, as is known to those skilled in the art.
- a longitudinal slot (not shown) may be provided in either the inner surface of the sheath or the outer surface of the bumper adjacent the side ports.
- FIGS. 3A-3E a method is shown for forming a rounded bullet-shaped distal portion 18 on a tubular sheath 12 and the like.
- a tubular sheath 12 is provided that is formed from substantially flexible plastic material, such as those described above, preferably pebax, and that has a lumen 16 therein extending from the distal end 14 towards the proximal end (not shown).
- the sheath 12 initially has a distal end 14 that terminates in a substantially blunt distal edge 19 ( FIG. 3A ).
- the sheath 12 has a plurality of segments having varying degrees of flexibility, for example, including a distal portion 18 , an intermediate portion (not shown), and a proximal portion (also not shown).
- the distal portion 18 is a predetermined length of pebax tubing that is thermal bonded, e.g., butt bonded to the intermediate portion, which is a predetermined length of pebax tubing reinforced by a stainless steel braid, such as the lengths described above.
- the intermediate portion is thermally bonded to a predetermined length of nylon tubing.
- an adhesive, connectors, and the like may be used to attach two or more of the portions to one another.
- the sheath 12 is pre-assembled, i.e., with the distal, intermediate, and proximal portions bonded to one another before the distal portion 18 is formed into its bullet shape, as described below.
- the distal portion 18 may be formed into its bullet shape and/or other steps of the method performed before the distal portion 18 is attached to the intermediate portion.
- a stent 50 or other prosthesis is disposed within the lumen 16 , preferably a predetermined distance from the distal end 14 of the sheath 12 .
- the stent 50 is constrained in its contracted condition, and inserted into the distal end 14 of the sheath 12 before the distal portion 18 is formed into its bullet shape.
- the stent 50 may be provided in its contracted condition, and introduced into the lumen 16 from the proximal end of the sheath 12 , e.g., either before or after the distal portion 18 is formed into its bullet shape.
- the stent 50 is a self-expanding tubular member formed from Nitinol having a transition temperature between ambient and body temperatures.
- the stent 50 may be formed into its enlarged condition in its austentic phase (e.g. by hand rolling for a coiled-sheet stent) and heat treated to set the enlarged condition in its shape memory.
- the stent 50 may then be chilled to its martensitic phase, e.g., at a temperature below ambient temperature, and preferably between about 0-10 degrees Celsius, for example, by blowing liquid Nitrogen onto the stent 50 .
- the stent 50 may then be pulled through one or more draw-down fixtures, i.e., tapered tubular dies (not shown), which may be chilled, to plastically compress the stent 50 into a contracted condition.
- the stent 50 preferably has a diameter substantially smaller than the lumen 16 of the sheath 12 .
- the stent 50 may then be pulled from the draw-down fixture into the lumen 16 of the sheath 12 .
- a teflon tubular guide or sheath may be used to facilitate sliding the stent 50 through one or more of the draw-down fixtures.
- the stent 50 may be pulled into the teflon guide as it enters a draw-down fixture, the teflon guide being split or otherwise removed from the stent 50 before it is pulled into the sheath 12 .
- the bumper member 30 (not shown in FIGS. 3A-3C ) may be inserted into the lumen 16 of the sheath 12 until the extension element 44 approaches, but does not extend from, the distal end 14 of the sheath 12 .
- the blunt edge 42 of the bumper element 40 may abut the proximal end 52 of the stent 50 , with the extension element 44 extending therethrough.
- the bumper member 30 may not be extended distally to abut the stent 50 until after the distal portion 18 is formed into its bullet shape.
- the bumper member 30 may not be introduced into the sheath 12 until after the distal portion 18 is formed into its bullet shape.
- a die 60 e.g., a spherically shaped “hot die,” is provided having a bore or other recess 62 therein.
- the bore 62 has an entry 64 with a cross-section substantially similar to the cross-section of the sheath 12 , a rounded inner end 66 having a tapered shape corresponding to the desired shape of the rounded distal portion 18 ( FIG. 3C ), and a relatively narrow aperture 67 extending distally from the inner end 66 through the die 60 .
- the die 60 may be coupled to a heating element in a conventional manner such that the die 60 may be heated to a desired temperature, as is well known in the art.
- the die 60 is heated to a temperature in excess of a melting point of the material from which the distal portion 18 of the sheath 12 is formed, for example, between about 150-200 degrees Celsius (about 300-400 degrees Fahrenheit), and preferably about 160 degrees Celsius (320 degrees Fahrenheit).
- a bullet 70 is inserted a predetermined distance into the distal end 14 of the sheath 12 , i.e., such that the bullet 70 does not contact the stent 50 (shown in FIG. 3B ) but provides sufficient sheath material beyond a distal end 72 of the bullet 70 to form the bullet-shaped distal portion 18 .
- a wire or other filament 73 is attached to the bullet 70 that extends distally from the distal end 72 of the bullet 70 .
- the bullet 70 and die 60 may be formed from like materials, preferably a hardened and polished tool steel.
- the distal end 72 of the bullet 70 has a predetermined curved shape corresponding to the rounded inner end 66 of the bore 62 in the die 60 .
- the filament 73 is guided through the aperture 67 , maintaining sufficient tension to keep the filament 73 taut, but without pulling the bullet 70 from the tubular member 12 .
- the distal portion 18 of the tubular member 12 is inserted into the bore 62 of the heated die 60 until the distal portion 18 of the tubular member 12 is softened and deformed to fill the cavity defined between the distal end 72 of the bullet 70 and the rounded inner end 66 of the bore 62 .
- the distal portion 18 is molded into a rounded bullet shape, the molded shape being defined by the distal end 72 of the bullet 70 and the rounded inner end 66 of the bore 62 in the die 60 .
- the resulting bullet shaped distal portion 18 includes the relatively small opening 25 (not shown in FIG. 3B ) therethrough corresponding to the filament 73 for accommodating a guidewire or bumper extension element (not shown).
- the sheath 12 may be removed from the bore 62 of the die 60 , and allowed to cool for sufficient time to substantially solidify the sheath, i.e., to return to its flexible, but solid state.
- One or more slits 34 are then formed in the tapered region 22 of the distal portion 14 .
- a cutting device (not known) is used that includes three cutting wires or blades that are equally spaced radially about a central axis. The cutting device is aligned with the longitudinal axis 28 of the sheath 12 and forced into the enclosed distal portion 18 until the cutting device cuts completely through the material of the enclosed distal portion 18 . The cutting device is then withdrawn, thereby providing a plurality of substantially independently flexible leaflets 24 on the distal portion 18 . As shown in FIG.
- the bullet 70 may then be removed from the distal portion 18 , e.g., by pulling on the filament 73 to deflect the leaflets 24 and withdraw the bullet 70 through the opening 26 .
- the leaflets 24 preferably resiliently return to their closed position upon removal of the bullet 70 , as shown in FIG. 3E , thereby defining the opening 25 .
- the filament 73 and aperture 67 may be eliminated from the bullet 70 and die 60 , and the bullet 70 withdrawn from the formed sheath 12 using other methods.
- a cutting device including a single blade or wire may be oriented substantially perpendicular to the longitudinal axis 28 of the sheath 12 , and a plurality of individual transverse slits may be cut into the distal portion 18 .
- individual leaflets may be formed using a multi-cavity tool, and the leaflets may be shaped into a final position, as will be appreciated by those skilled in the art.
- the bumper member 30 may be advanced further distally to push the stent 50 into a desired position within the lumen 16 of the sheath 12 , i.e., proximate the bullet-shaped distal portion 18 , and/or to direct the extension element 44 through the opening 25 .
- it may b desirable to form the distal portion 18 of the sheath 12 from a substantially transparent material, thereby facilitating visual monitoring of the stent 50 and/or the bumper member 30 .
- the apparatus 10 is then ready to be used to introduce and implant the stent 50 within a body lumen of a patient, as described further below.
- the stent 50 may be inserted into the sheath 12 from its proximal end after the distal portion 18 is formed into its bullet shape.
- the stent 50 may be constrained in its contracted condition, and advancing it through the lumen 16 of the tubular member 12 to the distal portion 18 .
- the stent may be released, i.e., unconstrained, once introduced into the lumen 16 , whereupon the stent may partially expand to engage the wall of the lumen 16 .
- the stent remains slidable within the lumen 16 such that the stent 50 may be advanced to a location proximate the distal portion 18 and/or easily deployed through the opening 26 .
- the bumper member 30 may be inserted into the proximal end of the sheath 12 and directed distally to advance the stent 50 to the desired position.
- the apparatus 10 may be used to implant the stent 50 or other prosthesis within a body lumen 100 of a patient, such as within a coronary, carotid, cerebral, renal artery, or other blood vessel.
- the apparatus 10 is percutaneously introduced into the patient's vasculature and advanced distally to a target treatment region 102 .
- the apparatus 10 is advanced over a guidewire 104 already placed across the treatment region 102 using conventional methods.
- the guidewire 104 may be backloaded through the extension element 44 , and through the bumper member 30 to its proximal end (not shown).
- the rounded distal portion 18 of the sheath 12 substantially protects the stent 50 during advancement and/or allows atraumatic advancement of the apparatus 10 .
- the leaflets 24 are resiliently flexible and biased to the closed position, causing the leaflets 24 to hug the guidewire 104 during advancement, particularly through tortuous anatomy.
- the leaflet(s) 24 on the outside of a sharp bend may hug the guidewire 104 , rather than deflecting away from the guidewire 104 and risking catching on the wall of the vessel, and possibly damaging the wall and/or dislodging embolic material from the wall.
- the rounded distal portion 18 may facilitate advancement of the apparatus 10 through the treatment region 100 .
- the stent 50 is positioned across the treatment region 102 , as shown in FIG. 4A , for example, by monitoring the marker 48 using fluoroscopy and the like.
- the treatment region 102 is a stenotic or occluded region of a blood vessel, although other lesions or damaged vessel segments may be treated, as will be appreciated by those skilled in the art.
- the leaflets 24 easily deflect outward to allow the stent 50 to be deployed through the opening 26 , and slide over the stent 50 and/or over the bumper member 30 .
- the apparatus 10 may be withdrawn from the body lumen 100 and from the patient (not shown).
- the sheath 12 remains in its retracted position without requiring advancement back over the bumper element 40 and/or the extension element 44 before removal of the apparatus 10 .
- the leaflets 24 preferably hug the outside of the bumper member 30 , thereby facilitating substantially atraumatic withdrawal of the apparatus 10 .
- the stent 50 is self-expanding, and therefore automatically expands upon deployment to engage the body lumen 100 at the treatment location 102 .
- the stent 50 may trap embolic material between itself and the body lumen 100 and/or may dilate and hold the body lumen 100 open.
- an expansion device such as a catheter (not shown) may be introduced into the body lumen 100 , e.g., upon removal of the apparatus 10 , and positioned within the stent 50 .
- a balloon or other expandable member on the catheter may be expanded to engage and further expand the stent 50 to a predetermined diameter, e.g., corresponding substantially to the unobstructed diameter of the body lumen 100 .
- the stent 50 may be plastically expandable, and may be mounted onto a catheter that is inserted into a sheath 12 in accordance with the present invention.
- the catheter may include a balloon or other expandable member over which the stent may be mounted.
- the expandable member may be expanded, e.g., by inflating the balloon, to plastically deform the stent and expand it to engage the body lumen at the treatment region.
- the expandable member may be deflated, and the apparatus withdrawn from the body lumen and the patient.
- other deployable devices may be provided within a sheath in accordance with the present invention, such as an electrode device, e.g., an array of electrodes on an expandable basket assembly and the like.
- an electrode device e.g., an array of electrodes on an expandable basket assembly and the like.
- the sheath may be retracted with respect to the underlying device, until one or more elements on the device are deployed from the sheath.
- a procedure may be completed at the location, e.g., an ablation procedure, and then the sheath and device may be withdrawn from the location.
Abstract
An apparatus for delivering a stent into a blood vessel includes a sheath having a rounded bullet-shaped distal portion including a plurality of flexible leaflets integrally molded thereto. The stent is disposed in its contracted condition within a lumen of the sheath proximate the distal portion. A bumper is slidably disposed within the lumen that includes a helical compression coil, a bumper element attached to the helical coil including a blunt distal edge for abutting the stent, and an extension element extending distally from the bumper element through the stent and between the leaflets to facilitate introducing the apparatus over a guidewire. The sheath is formed by inserting a bullet into a blunt-ended tube, and inserting the tube into a bullet-shaped bore in a heated die until the tube material is softened and deforms into a rounded bullet shape. Slits are then cut into the distal portion to create the leaflets.
Description
- This application is a continuation of application Ser. No. 09/664,970, filed Sep. 18, 2000, the disclosures of which is expressly incorporated herein by reference.
- The present invention relates generally to apparatus and methods for delivering endoluminal prostheses within body lumens of a patient, and more particularly to apparatus for delivering tubular prostheses or “stents” within a patient's vasculature for treating stenoses or other lesions, for example, within the coronary and carotid arteries, and to methods of making and using such apparatus.
- In recent years, a number of minimally invasive technologies have been developed for treating diseases, such as atherosclerosis, that result in narrowing of blood vessels, for example, within the coronary or carotid arteries. Tubular prostheses or “stents” have been developed for maintaining the patency of a blood vessel, for example, following angioplasty or other procedures used to treat a stenosis, occlusion, or other lesion within the blood vessel. The stent may be implanted across a treatment site to scaffold the site and prevent it from subsequently contracting or otherwise becoming obstructed.
- Generally, the stent may be placed upon a catheter in a contracted condition, and the catheter advanced endoluminally to the treatment site until the stent is positioned across the stenosis. The stent may then be deployed and substantially anchored at the treatment site. The stent may be self-expanding, i.e., may be biased to expand to an enlarged condition upon release from the delivery catheter, thereby automatically substantially anchoring the stent at the treatment site. Alternatively, the stent may be plastically deformable, i.e., may be expanded with the aid of a balloon, which may underlie the stent on the catheter. The balloon may be inflated to expand the stent from the contracted condition to the enlarged condition wherein the stent substantially engages the wall of the treatment site. A balloon, for example, on a separate balloon catheter, may also be used to further expand and/or anchor a self-expanding stent.
- Similarly, for ablation procedures and the like, a catheter including an array of electrodes, for example, on an expandable basket assembly, may be provided. The device may be introduced into a body lumen, e.g., through the patient's vasculature into the heart, to treat conditions, such as heart arrhythmia.
- With any of these devices, a sheath may be provided over the catheter to protect the elements on the distal end of the catheter, such as a stent, a balloon, and/or an array of electrodes. The sheath may be advanced distally over the proximal end of the catheter until it covers the distal end and the element(s) thereon, or the distal end of the catheter may be introduced into the sheath, and advanced until it is proximate the distal end of the sheath. The distal end of the catheter, with the overlying sheath thereon, may then be introduced into a patient and positioned at a treatment site, whereupon the sheath may be retracted to expose the distal end of the catheter. After treatment, the sheath may be advanced back over the distal end of the catheter, and the entire device withdrawn from the patient.
- One of the problems associated with these devices is that they may have substantially blunt distal ends that may scrape along the wall of a vessel during advancement therethrough, possibly damaging the wall and/or dislodging embolic material from the wall. To facilitate atraumatic advancement, particularly through tortuous anatomy, transition tips have been suggested for these devices.
- For example, a conical or tapered nosepiece may be provided on the distal end of the catheter. A sheath may be disposed over the catheter, for example, to substantially cover the stent or other underlying element, such that the nosepiece extends distally from the end of the sheath, a distal edge of the sheath abutting the nosepiece. The nosepiece may facilitate advancement of the device through a narrow region of a blood vessel, although it may also risk catching on the wall of the vessel and/or dislodging embolic material, e.g., between the distal edge of the sheath and the nosepiece. Following delivery of a stent from the device, the nosepiece is generally positioned distal to the treated lesion. If the nosepiece is withdrawn directly, the proximal edge of the nosepiece may catch on the stent struts, resulting in the potential for trauma and embolic debris release. Alternatively, the sheath may be re-advanced across the treatment site to “recapture” the nosepiece, although in this approach the distal edge of the sheath may also catch on the stent struts.
- As an alternative to a tapered nosepiece, a sheath having a rounded distal end has been suggested, as disclosed in U.S. Pat. No. 5,593,412 issued to Martinez et al. Weakened areas or slits are provided in the distal end, thereby defining sections that may be softened upon introduction of warm saline solution. Once the sections are softened, the sheath may be retracted from an underlying balloon catheter to expose and implant a stent mounted on the catheter. Introduction of saline or other liquids into a patient's vasculature, however, may be undesirable, but is necessary in order to soften the sections on the distal end of the sheath and allow the stent to be deployed from the sheath.
- Another problem associated with such delivery systems is that the sheaths and/or catheters may buckle during insertion, because of the distal force applied from the proximal end to advance them through the patient's vasculature. In addition, because of their tubular nature, they may kink when advanced through tortuous anatomy, possibly damaging the device or an element within the device.
- Accordingly, it is believed that delivery systems that facilitate delivery of a stent through a patient's vasculature and/or that overcome the problems discussed above would be considered useful.
- The present invention is directed to apparatus for delivering treatment elements, such as tubular prostheses or “stents,” within a body lumen of a patient, for example, for treating stenoses or other lesions within the coronary arteries, the carotid arteries, or other blood vessels, and to methods of making and using such apparatus.
- In accordance with one aspect of the present invention, an apparatus is provided for delivering a prosthesis into a blood vessel of a patient that includes an elongate tubular member having a proximal end, a distal end, and a lumen extending between the proximal and distal ends. The distal end has a size for endoluminal insertion into a blood vessel and terminates in a substantially atraumatic distal portion including a plurality of flexible leaflets integrally molded thereto.
- The leaflets are deflectable from a closed position wherein the leaflets engage one another to an open position wherein the leaflets define an opening communicating with the lumen. Preferably, the leaflets define a substantially rounded bullet shape in the closed position, although alternatively, the leaflets may define a substantially conical shape in the closed position. The leaflets are preferably substantially flexible and independently deflectable at a temperature less than body temperature, and are biased towards the closed position, but are resiliently deflectable to the open position. Adjacent leaflets may be separated by a slit, or may be connected to one another by weakened regions, the weakened regions being tearable upon retraction of the tubular member with respect to the prosthesis to allow the leaflets to be deflected towards the open position.
- In a preferred embodiment, a tubular prosthesis is disposed within the lumen proximate the distal portion. An elongate bumper member having a proximal end and a distal end is also provided, the bumper member being slidably disposed within the lumen of the sheath. The distal end of the bumper member has a blunt edge disposed adjacent to the proximal end of the prosthesis for preventing axial displacement of the prosthesis upon retraction of the tubular member with respect to the bumper member and/or the prosthesis.
- Preferably, the prosthesis comprises a self-expanding stent, such as a coiled-sheet stent, the stent being biased to assume an expanded condition having a cross-section larger than the lumen of the tubular member, and being compressible to a contracted condition to facilitate insertion into the lumen.
- In accordance with another aspect of the present invention, an apparatus for delivering a prosthesis into a blood vessel of a patient is provided that includes an elongate tubular member, such as that described above, having a proximal end, a distal end, and a lumen extending between the proximal and distal ends, the distal end having a size for endoluminal insertion into a blood vessel. A tubular prosthesis is disposed within the lumen proximate the distal end. An elongate bumper member is also provided that includes a helical coil having a proximal end and a distal end, the bumper member being slidably disposed within the lumen of the sheath. The distal end of the bumper member has a blunt distal edge disposed adjacent a proximal end of the prosthesis for preventing axial displacement of the prosthesis upon retraction of the tubular member with respect to the bumper member.
- In a preferred embodiment, the bumper member includes a helical wire compression coil, preferably a solid height coil, extending between its proximal and distal ends. A plastic bumper element extends from a distal end of the helical coil, the bumper element including the blunt distal edge thereon. An extension element extends distally from the bumper element, the extension element having a cross-section substantially smaller than the bumper element, whereby the extension element may extend through the prosthesis disposed within the lumen of the tubular member. The helical coil, bumper element, and/or the extension element include a lumen extending axially therethrough for receiving a guidewire therethrough.
- In accordance with yet another aspect of the present invention, a method for making a sheath for delivering a treatment element within a body lumen of a patient is provided. A tubular member is provided that is formed from a substantially flexible material, the tubular member having a proximal end, a distal end, and a lumen extending axially between the proximal and distal ends, the distal end having a size for endoluminal insertion into a body lumen. A die is provided having a bore therein, the bore having a tapered shape. The die is heated to a temperature in excess of a melting point of the flexible material from which the tubular member is formed. The distal end of the tubular member is inserted into the bore of the heated die until a distal portion of the tubular member is softened and deformed into a tapered shape substantially enclosing the distal end. One or more slits are then created in the distal portion of the tubular member after it is deformed into the tapered shape, the slits defining a plurality of leaflets. A treatment element may be inserted into the lumen of the tubular member until it is disposed proximate the distal portion.
- In a preferred method, a bullet having a tapered shape distal end is inserted into the distal end of the tubular member before inserting the distal end of the tubular member into the bore. Preferably, the bullet and the bore have corresponding substantially rounded shapes defining a mold cavity therebetween when the distal end of the tubular member is inserted into the bore.
- In another preferred method, the treatment element is a tubular prosthesis for implantation within a body lumen of a patient. Preferably, the prosthesis is a self-expanding stent biased to assume an expanded condition having a cross-section larger than the lumen, and compressible to a contracted condition before being inserted into the lumen of the tubular member. The prosthesis may be inserted into the lumen of the tubular member before inserting the distal end of the tubular member into the bore, e.g., inserted into the lumen from the distal end of the tubular member. Alternatively, the prosthesis may be inserted into the lumen from the proximal end of the tubular member, e.g., either before or after the leaflets are formed on the distal portion of the tubular member.
- An elongate bumper member may be inserted into the lumen of the tubular member, the bumper member being slidably disposed within the lumen of the tubular member, the distal end having a blunt distal edge for abutting a proximal end of the prosthesis. To make the bumper member, an elongate helical coil may be provided having a proximal end and a distal end. A tubular bumper element may be attached to the distal end of the helical coil to provide the bumper member, the bumper element including the blunt distal edge of the bumper element. Preferably, the bumper element is formed from plastic, and is attached to the helical coil by heating the bumper element until it is softened, and then directing the softened bumper element over the distal end of the helical coil. A tubular extension element may be attached to the bumper element, the extension element having a cross-section substantially smaller than the bumper element.
- Other objects and features of the present invention will become apparent from consideration of the following description taken in conjunction with the accompanying drawings.
-
FIG. 1A is a cross-sectional side view of a sheath having a rounded distal tip, in accordance with the present invention. -
FIG. 1B is a cross-sectional side view of an apparatus for delivering a stent, including the sheath ofFIG. 1A . -
FIGS. 2A and 2B are end views of the sheath ofFIGS. 1A and 1B , respectively. -
FIGS. 3A-3E are cross-sectional views showing a method for forming a rounded distal tip on a sheath, such as that shown inFIG. 1A . -
FIGS. 4A and 4B are cross-sectional views of a body lumen, showing a method for implanting a stent using an apparatus in accordance with the present invention. - Turning now to the drawings,
FIGS. 1A-2B show a preferred embodiment of anapparatus 10 for delivering a stent or othertubular prosthesis 50 into a blood vessel or other body lumen of a patient (not shown). Generally, theapparatus 10 includes an elongatetubular sheath 12 having a proximal end (not shown), adistal end 14, and alumen 16 extending generally therebetween. Thetubular sheath 12 may be formed from a substantially flexible or semi-rigid material that may facilitate its advancement within a body lumen of a patient, preferably within the vasculature of a patient. - For example, the
sheath 12 may be formed from a polymer, such as pebax, polyethylene, urethane, nylon, or other plastic material, that may be extruded or molded into elongate tubing of a desired length. Preferably, the tubing has a wall thickness of between about 0.003-0.006 inch (0.075-0.150 mm), and has a substantially uniform outer diameter appropriate for the size of the stent being implanted, for example, between about 1.5-2.5 mm. Thesheath 12 may have a substantially uniform construction along its length, or thesheath 12 may include portions along its length having varying degrees of flexibility. - In a preferred embodiment, the
sheath 12 includes adistal portion 18 formed entirely from a substantially flexible material, such as pebax, and anintermediate portion 20 formed from pebax including astiffening element 22 therein. For example, theintermediate portion 20 may include a braid or mesh, e.g., of stainless steel, laid over a teflon liner, with pebax tubing formed over the braid. Alternatively, the stiffeningelement 22 may be a helical wire coil and the like molded or otherwise formed in the tubing. The stiffeningelement 22 may enhance a rigidity of theintermediate portion 20, for example, to reduce the risk of theintermediate portion 20 buckling or kinking, while still providing flexibility transverse to thelongitudinal axis 28, e.g., to accommodate advancement through tortuous anatomy. Preferably, thesheath 12 also includes a proximal portion (not shown) that is formed from a more rigid material, such as nylon tubing, that may include a stiffening element as described above. In a preferred embodiment, thedistal portion 18 has a length of between about 10-20 cm, theintermediate portion 20 has a length of between about 20-30 cm, and the proximal portion has a length of between about 85-120 cm, more preferably about 100 cm or more. - The
distal portion 18 of thesheath 12 preferably has a rounded bullet shape defined by a plurality offlexible leaflets 24 that are integrally formed thereon. Theleaflets 24 are preferably deflectable from a closed position, whereinadjacent leaflets 24 abut one another, to an open position. In the closed position, theleaflets 24 substantially close thelumen 16, as shown inFIG. 2A . Preferably, in the closed position, theleaflets 24 define a relativelysmall opening 25 where their apices meet. In the open position (theleaflets 24 are shown only partially open inFIG. 2B ), theleaflets 24 are spread apart to define anopening 26 communicating with thelumen 16. Preferably, in the open position, theleaflets 24 are oriented substantially axially such that theopening 26 has a cross-section similar to thelumen 16. In the preferred embodiment shown inFIGS. 2A and 2B , threeleaflets 24 are provided, although additional leaflets may be provided if desired. - As best seen in
FIG. 1A , in the closed position, theleaflets 24 preferably define a substantially atraumaticdistal portion 18 that may facilitate advancement of thesheath 12 endoluminally within a patient's vasculature with minimal risk of dislodging embolic material from and/or otherwise damaging the wall of a body lumen through which thesheath 12 is advanced. In the preferred embodiment shown, theleaflets 24 define a substantially rounded bullet shape in the closed position. Alternatively,leaflets 24 defining a substantially conical shape (not shown) in the closed position may be provided, with theleaflets 24 preferably biased to the closed position, as described below. - The
leaflets 24 are substantially flexible and independently deflectable substantially independent of the temperature to which theleaflets 24 are exposed, e.g., at a temperature substantially less than body temperature. In a preferred embodiment, theleaflets 24 are biased towards the closed position, but are resiliently deflectable to the open position. This may ensure that theopening 26 remains substantially closed until time of deployment of an element, such asstent 50, from within thelumen 16, and/or that theleaflets 24 do not catch on anything and open inadvertently. This may be particularly important when theapparatus 10 is advanced through tortuous anatomy, as described further below. Alternatively, theleaflets 24 may be at least partially plastically deformed when they are deflected from the closed position to the open position. In this alternative, theleaflets 24 may not return completely to the closed position when released from the fully open position, e.g., after thestent 50 is deployed from theapparatus 10. - Preferably,
adjacent leaflets 24 are separated by a relativelynarrow slit 28, although alternatively, theleaflets 24 may partially overlap with one another in the closed position. In a further alternative, adjacent leaflets may be separated by a thin-walled or weakened region (not shown) that may be easily tearable upon retraction of thesheath 12 with respect to a stent or other element being deployed from within thelumen 16. Once the weakened regions are torn, the leaflets may be freely deflected towards the open position as the element is being deployed. - In addition, the
leaflets 24 may have a thickness that is substantially thinner than a wall thickness of the rest of thedistal portion 18, preferably tapering towards theirdistal tips 24 a as shown inFIGS. 1A and 1B , thereby enhancing the flexibility of theleaflets 24. The tapering thickness may also ensure that theleaflets 24 are biased towards the closed position, yet may deflect easily to accommodate a guidewire (not shown), bumper extension element, and the like, as described further below. - Returning to
FIG. 1B , in a preferred embodiment, theapparatus 10 also includes anelongate bumper member 30 that is slidably disposed within thesheath 12. Thebumper member 30 preferably includes a proximal end (not shown), adistal end 32, and alumen 34 that extends therebetween. Thebumper member 30 preferably has a substantially uniform outer diameter slightly smaller than theinterior lumen 16 of thesheath 12, preferably by about 0.003-0.005 inch (0.075-0.125 mm) to create a close sliding, but not interfering, fit between thebumper member 30 and thesheath 12. Thelumen 34 has a diameter sufficiently large to accommodate a guidewire (not shown) therethrough, preferably between about 0.015-0.020 inch (0.375-0.500 mm), and more preferably about 0.016 inch (0.400 mm). - In a preferred form, the
bumper member 30 is formed from a helicalwire compression coil 36, e.g., having adjacent turns that substantially abut one another. Thecoil 36 may be formed from flat or round wire, e.g., of stainless steel and the like, that is continuously helically wound along the length of thebumper member 30, preferably a solid height coil. A relatively thin layer ofteflon 38 and the like may be provided around the outside of thecoil 36 to enhance a sliding relationship between thebumper member 30 and thesheath 12. Because of thecoil 36, thebumper member 30 may be substantially resistant to buckling or kinking, while facilitating bending of thebumper member 30 transverse to thelongitudinal axis 28. - A substantially rigid tubular segment (not shown) may be attached to or otherwise extend from the proximal end of the
coil 36. Preferably, the tubular segment is a section of hypotube having an inner lumen (not shown) similar to thelumen 34 of thecoil 36, and more preferably a two-stage length of hypotube that has a greater outer diameter on its proximal-most end. The tubular segment may facilitate distal advancement of thebumper member 30 into thesheath 12 with minimal risk of buckling and/or may provide enhanced tactile perception of relative movement of thebumper member 30 and thesheath 12. A valve or other seal (not shown), e.g., for accommodating a guidewire therethrough while maintaining a fluid-tight seal, may also be provided on the proximal end of the tubular segment. - The
bumper member 30 also includes atubular bumper element 40 on adistal end 37 of thecoil 36 that includes a substantially bluntdistal edge 42. Thebumper element 40 is preferably formed from pebax or other plastic material. Aplastic bumper element 40 ensures no metal-to-metal contact, e.g., between thecoil 36 of thebumper member 30 and thestent 50 that may lead to corrosion of the stent material. In addition, pebax and other substantially flexible materials may deform slightly, e.g., when thesheath 12 is retracted, to enhance contact between the bluntdistal edge 42 of thebumper element 40 and thestent 50. Thebumper element 40 is preferably attached to thedistal end 37 of thecoil 36, e.g., by heating thebumper element 40 to soften it and directing it over thedistal end 37, such that the bumper element is fused into the coils adjacent thedistal end 37. - The
bumper member 30 may also include a radiopaque orother marker 48 thereon for identifying a location of thebumper member 30 using external imaging, such as fluoroscopy. Preferably, aplatinum iridium ring 48 is provided on thebumper element 40 immediately adjacent the bluntdistal edge 42, thereby identifying a position of theproximal end 52 of thestent 50. Alternatively, a marker (not shown) may be provided elsewhere on theapparatus 10 in addition to or instead of themarker 48, such as on thesheath 12 or thestent 50 itself. Thus, themarker 48 may facilitate positioning of theapparatus 10, and more particularly thestent 50 or other element therein, axially within a body lumen (not shown) before deploying the element from within thesheath 12, as described further below. - The
bumper member 30 may also include atubular extension element 44 that is thermally bonded or otherwise attached to and extends distally from thebumper element 40. Theextension element 44 has an outer diameter that is substantially smaller than thebumper element 40 For example, theextension element 44 may be partially inserted into thebumper element 40 as it is thermally bonded thereto so as not to interfere with theblunt edge 42 of thebumper element 40. Preferably, theextension element 44 has an outer diameter of about 0.66 mm (0.026 inch) to facilitate its insertion through thestent 50, an inner diameter of about 0.41 mm (0.016 inch) to accommodate a guidewire therethrough, and a length of about 25 mm (1.0 inch). Theextension element 44 may be appropriately sized larger or smaller to accommodate a guidewire, for example, between about 0.009-0.038 in (0.225-0.95 mm). Theextension element 44 is preferably substantially flexible and has a substantially smooth outer surface to provide a low-friction, sliding contact with an element disposed within thesheath 12. - In a preferred embodiment, a
stent 50 or other tubular prosthesis or graft may be disposed within thelumen 16 of thesheath 12 proximate thedistal portion 18. Thestent 50 preferably is expandable between a contracted condition that facilitates its loading into thelumen 16 of thesheath 12, and an enlarged condition for engaging a wall of a blood vessel or other body lumen (not shown). In a preferred embodiment, thestent 50 is a coiled-sheet stent, such as that disclosed in U.S. Pat. No. 5,443,400 issued to Sigwart, and/or in co-pending applications Ser. No. 09/347,845, filed Jul. 2, 1999, and Ser. No. 09/406,984, filed Sep. 28, 1999, the disclosures of which are incorporated herein by reference. Thestent 50 may be self-expanding, i.e., may be biased to assume the enlarged condition, but may be compressed and constrained in the contracted condition, for example, by thelumen 16 of thesheath 12. Alternatively, thestent 50 may be plastically defonnable, i.e., may be substantially relaxed in the contracted condition, but may be forcibly expanded to the enlarged condition, for example, using a balloon catheter, as is known in the art. - Preferably, the
apparatus 10 is provided pre-assembled with thestent 50 disposed within thelumen 16 of thesheath 12 adjacent thedistal portion 18 of the sheath in its contracted condition. Thebumper member 30 is also disposed within thelumen 16 such that theblunt edge 42 of thebumper element 40 is adjacent aproximal end 52 of thestent 50. Theextension element 44 preferably extends distally through thestent 50 and through theleaflets 24, as best seen inFIGS. 1B and 2B . Theextension element 44 may facilitate insertion of a guidewire (not shown) through theapparatus 10, i.e., through thelumen 16 of thesheath 12 into thelumen 34 of thebumper member 30 to a proximal end of theapparatus 10. Preferably, theopening 25 at the apices of theleaflets 24 accommodates theextension element 44 therethrough without causing theleaflets 24 to partially buckle or bulge. - Alternatively, the
extension element 44 may be eliminated, and a guidewire inserted directly between theleaflets 24 into thelumens apparatus 10 may be used to implant thestent 50 within a body lumen, preferably within a carotid artery, a coronary artery, a cerebral artery, a renal artery, or other blood vessel, as described further below. In a further alternative, theapparatus 10 may incorporate “rapid exchange” configurations where a guidewire may exit from thelumens sheath 12 and/orbumper member 30 through side ports (not shown) at a location along their lengths, i.e., at an intermediate location, rather than at their proximal ends, as is known to those skilled in the art. To accommodate a guidewire between thesheath 12 and thebumper member 30 during retraction, a longitudinal slot (not shown) may be provided in either the inner surface of the sheath or the outer surface of the bumper adjacent the side ports. - Turning to
FIGS. 3A-3E , a method is shown for forming a rounded bullet-shapeddistal portion 18 on atubular sheath 12 and the like. Atubular sheath 12 is provided that is formed from substantially flexible plastic material, such as those described above, preferably pebax, and that has alumen 16 therein extending from thedistal end 14 towards the proximal end (not shown). Thesheath 12 initially has adistal end 14 that terminates in a substantially blunt distal edge 19 (FIG. 3A ). - In a preferred embodiment, the
sheath 12 has a plurality of segments having varying degrees of flexibility, for example, including adistal portion 18, an intermediate portion (not shown), and a proximal portion (also not shown). Preferably, thedistal portion 18 is a predetermined length of pebax tubing that is thermal bonded, e.g., butt bonded to the intermediate portion, which is a predetermined length of pebax tubing reinforced by a stainless steel braid, such as the lengths described above. The intermediate portion, in turn, is thermally bonded to a predetermined length of nylon tubing. Alternatively, an adhesive, connectors, and the like may be used to attach two or more of the portions to one another. - Preferably, the
sheath 12 is pre-assembled, i.e., with the distal, intermediate, and proximal portions bonded to one another before thedistal portion 18 is formed into its bullet shape, as described below. Alternatively, thedistal portion 18 may be formed into its bullet shape and/or other steps of the method performed before thedistal portion 18 is attached to the intermediate portion. - A
stent 50 or other prosthesis is disposed within thelumen 16, preferably a predetermined distance from thedistal end 14 of thesheath 12. Preferably, thestent 50 is constrained in its contracted condition, and inserted into thedistal end 14 of thesheath 12 before thedistal portion 18 is formed into its bullet shape. Alternatively, thestent 50 may be provided in its contracted condition, and introduced into thelumen 16 from the proximal end of thesheath 12, e.g., either before or after thedistal portion 18 is formed into its bullet shape. - In a preferred embodiment, the
stent 50 is a self-expanding tubular member formed from Nitinol having a transition temperature between ambient and body temperatures. Thestent 50 may be formed into its enlarged condition in its austentic phase (e.g. by hand rolling for a coiled-sheet stent) and heat treated to set the enlarged condition in its shape memory. Thestent 50 may then be chilled to its martensitic phase, e.g., at a temperature below ambient temperature, and preferably between about 0-10 degrees Celsius, for example, by blowing liquid Nitrogen onto thestent 50. Thestent 50 may then be pulled through one or more draw-down fixtures, i.e., tapered tubular dies (not shown), which may be chilled, to plastically compress thestent 50 into a contracted condition. In the contracted condition, thestent 50 preferably has a diameter substantially smaller than thelumen 16 of thesheath 12. Thestent 50 may then be pulled from the draw-down fixture into thelumen 16 of thesheath 12. In a preferred method, a teflon tubular guide or sheath (not shown) may be used to facilitate sliding thestent 50 through one or more of the draw-down fixtures. Thestent 50 may be pulled into the teflon guide as it enters a draw-down fixture, the teflon guide being split or otherwise removed from thestent 50 before it is pulled into thesheath 12. - The bumper member 30 (not shown in
FIGS. 3A-3C ) may be inserted into thelumen 16 of thesheath 12 until theextension element 44 approaches, but does not extend from, thedistal end 14 of thesheath 12. For example, theblunt edge 42 of thebumper element 40 may abut theproximal end 52 of thestent 50, with theextension element 44 extending therethrough. Alternatively, thebumper member 30 may not be extended distally to abut thestent 50 until after thedistal portion 18 is formed into its bullet shape. In a further alternative, thebumper member 30 may not be introduced into thesheath 12 until after thedistal portion 18 is formed into its bullet shape. - Returning to
FIGS. 3A-3C , adie 60, e.g., a spherically shaped “hot die,” is provided having a bore orother recess 62 therein. Thebore 62 has anentry 64 with a cross-section substantially similar to the cross-section of thesheath 12, a roundedinner end 66 having a tapered shape corresponding to the desired shape of the rounded distal portion 18 (FIG. 3C ), and a relativelynarrow aperture 67 extending distally from theinner end 66 through thedie 60. The die 60 may be coupled to a heating element in a conventional manner such that the die 60 may be heated to a desired temperature, as is well known in the art. In a preferred method, thedie 60 is heated to a temperature in excess of a melting point of the material from which thedistal portion 18 of thesheath 12 is formed, for example, between about 150-200 degrees Celsius (about 300-400 degrees Fahrenheit), and preferably about 160 degrees Celsius (320 degrees Fahrenheit). - As seen in
FIG. 3A , abullet 70 is inserted a predetermined distance into thedistal end 14 of thesheath 12, i.e., such that thebullet 70 does not contact the stent 50 (shown inFIG. 3B ) but provides sufficient sheath material beyond adistal end 72 of thebullet 70 to form the bullet-shapeddistal portion 18. Preferably, a wire orother filament 73 is attached to thebullet 70 that extends distally from thedistal end 72 of thebullet 70. Thebullet 70 and die 60 may be formed from like materials, preferably a hardened and polished tool steel. Thedistal end 72 of thebullet 70 has a predetermined curved shape corresponding to the roundedinner end 66 of thebore 62 in thedie 60. - In preparation for molding the
distal portion 18 of thesheath 12, thefilament 73 is guided through theaperture 67, maintaining sufficient tension to keep thefilament 73 taut, but without pulling thebullet 70 from thetubular member 12. As shown inFIG. 3B , thedistal portion 18 of thetubular member 12 is inserted into thebore 62 of theheated die 60 until thedistal portion 18 of thetubular member 12 is softened and deformed to fill the cavity defined between thedistal end 72 of thebullet 70 and the roundedinner end 66 of thebore 62. Thus, thedistal portion 18 is molded into a rounded bullet shape, the molded shape being defined by thedistal end 72 of thebullet 70 and the roundedinner end 66 of thebore 62 in thedie 60. Preferably, only slight pressure, e.g., mere hand pressure, preferably between about 1-2 pounds, is applied axially to thesheath 12 to fill the cavity defined by thebullet 70 and thebore 62 and ensure that there are no discontinuities in the resulting bullet shapeddistal portion 18. Because of thefilament 73, the resulting bullet shapeddistal portion 18 includes the relatively small opening 25 (not shown inFIG. 3B ) therethrough corresponding to thefilament 73 for accommodating a guidewire or bumper extension element (not shown). - As shown in
FIG. 3C , once the rounded bullet-shapeddistal portion 18 is formed, thesheath 12 may be removed from thebore 62 of the die 60, and allowed to cool for sufficient time to substantially solidify the sheath, i.e., to return to its flexible, but solid state. - One or
more slits 34 are then formed in the taperedregion 22 of thedistal portion 14. Preferably, a cutting device (not known) is used that includes three cutting wires or blades that are equally spaced radially about a central axis. The cutting device is aligned with thelongitudinal axis 28 of thesheath 12 and forced into the encloseddistal portion 18 until the cutting device cuts completely through the material of the encloseddistal portion 18. The cutting device is then withdrawn, thereby providing a plurality of substantially independentlyflexible leaflets 24 on thedistal portion 18. As shown inFIG. 3D , thebullet 70 may then be removed from thedistal portion 18, e.g., by pulling on thefilament 73 to deflect theleaflets 24 and withdraw thebullet 70 through theopening 26. Theleaflets 24 preferably resiliently return to their closed position upon removal of thebullet 70, as shown inFIG. 3E , thereby defining theopening 25. - Alternatively, the
filament 73 andaperture 67 may be eliminated from thebullet 70 and die 60, and thebullet 70 withdrawn from the formedsheath 12 using other methods. For even numbers of slits, a cutting device including a single blade or wire (not shown) may be oriented substantially perpendicular to thelongitudinal axis 28 of thesheath 12, and a plurality of individual transverse slits may be cut into thedistal portion 18. In alternative methods, individual leaflets may be formed using a multi-cavity tool, and the leaflets may be shaped into a final position, as will be appreciated by those skilled in the art. - Once the
leaflets 24 are formed, thebumper member 30 may be advanced further distally to push thestent 50 into a desired position within thelumen 16 of thesheath 12, i.e., proximate the bullet-shapeddistal portion 18, and/or to direct theextension element 44 through theopening 25. To facilitate this pre-loading stage, it may b desirable to form thedistal portion 18 of thesheath 12 from a substantially transparent material, thereby facilitating visual monitoring of thestent 50 and/or thebumper member 30. Theapparatus 10 is then ready to be used to introduce and implant thestent 50 within a body lumen of a patient, as described further below. - In an alternative method, the
stent 50 may be inserted into thesheath 12 from its proximal end after thedistal portion 18 is formed into its bullet shape. For example, thestent 50 may be constrained in its contracted condition, and advancing it through thelumen 16 of thetubular member 12 to thedistal portion 18. The stent may be released, i.e., unconstrained, once introduced into thelumen 16, whereupon the stent may partially expand to engage the wall of thelumen 16. Preferably, the stent remains slidable within thelumen 16 such that thestent 50 may be advanced to a location proximate thedistal portion 18 and/or easily deployed through theopening 26. Thebumper member 30 may be inserted into the proximal end of thesheath 12 and directed distally to advance thestent 50 to the desired position. - Turning to
FIGS. 4A and 4B , theapparatus 10 may be used to implant thestent 50 or other prosthesis within abody lumen 100 of a patient, such as within a coronary, carotid, cerebral, renal artery, or other blood vessel. Theapparatus 10 is percutaneously introduced into the patient's vasculature and advanced distally to atarget treatment region 102. Preferably, theapparatus 10 is advanced over aguidewire 104 already placed across thetreatment region 102 using conventional methods. Theguidewire 104 may be backloaded through theextension element 44, and through thebumper member 30 to its proximal end (not shown). - The rounded
distal portion 18 of thesheath 12 substantially protects thestent 50 during advancement and/or allows atraumatic advancement of theapparatus 10. Preferably, as explained above, theleaflets 24 are resiliently flexible and biased to the closed position, causing theleaflets 24 to hug theguidewire 104 during advancement, particularly through tortuous anatomy. For example, if theleaflets 24 are flexible and biased to the closed position, the leaflet(s) 24 on the outside of a sharp bend may hug theguidewire 104, rather than deflecting away from theguidewire 104 and risking catching on the wall of the vessel, and possibly damaging the wall and/or dislodging embolic material from the wall. In addition, the roundeddistal portion 18 may facilitate advancement of theapparatus 10 through thetreatment region 100. - Once the
apparatus 10 is advanced into thebody lumen 100, thestent 50 is positioned across thetreatment region 102, as shown inFIG. 4A , for example, by monitoring themarker 48 using fluoroscopy and the like. Preferably, thetreatment region 102 is a stenotic or occluded region of a blood vessel, although other lesions or damaged vessel segments may be treated, as will be appreciated by those skilled in the art. Once thestent 50 is properly positioned, thebumper member 30 is held stationary, and thesheath 12 withdrawn to deploy thestent 50 from thelumen 16, as shown inFIG. 4B . Because of their flexible nature, theleaflets 24 easily deflect outward to allow thestent 50 to be deployed through theopening 26, and slide over thestent 50 and/or over thebumper member 30. Once thestent 50 is deployed, theapparatus 10 may be withdrawn from thebody lumen 100 and from the patient (not shown). Preferably, thesheath 12 remains in its retracted position without requiring advancement back over thebumper element 40 and/or theextension element 44 before removal of theapparatus 10. Theleaflets 24 preferably hug the outside of thebumper member 30, thereby facilitating substantially atraumatic withdrawal of theapparatus 10. - Preferably, the
stent 50 is self-expanding, and therefore automatically expands upon deployment to engage thebody lumen 100 at thetreatment location 102. Thestent 50 may trap embolic material between itself and thebody lumen 100 and/or may dilate and hold thebody lumen 100 open. If desired to further expand thestent 50, an expansion device, such as a catheter (not shown) may be introduced into thebody lumen 100, e.g., upon removal of theapparatus 10, and positioned within thestent 50. A balloon or other expandable member on the catheter may be expanded to engage and further expand thestent 50 to a predetermined diameter, e.g., corresponding substantially to the unobstructed diameter of thebody lumen 100. - In an alternative embodiment (not shown), the
stent 50 may be plastically expandable, and may be mounted onto a catheter that is inserted into asheath 12 in accordance with the present invention. The catheter may include a balloon or other expandable member over which the stent may be mounted. Once the sheath is retracted to deploy the stent, for example, at a target treatment region, the expandable member may be expanded, e.g., by inflating the balloon, to plastically deform the stent and expand it to engage the body lumen at the treatment region. Once the stent has been expanded to a desired size, the expandable member may be deflated, and the apparatus withdrawn from the body lumen and the patient. - In further alternatives, other deployable devices may be provided within a sheath in accordance with the present invention, such as an electrode device, e.g., an array of electrodes on an expandable basket assembly and the like. Once a desired location is reached, such as a chamber of a heart, the sheath may be retracted with respect to the underlying device, until one or more elements on the device are deployed from the sheath. A procedure may be completed at the location, e.g., an ablation procedure, and then the sheath and device may be withdrawn from the location.
- While the invention is susceptible to various modifications, and alternative forms, specific examples thereof have been shown in the drawings and are herein described in detail. It should be understood, however, that the invention is not to be limited to the particular forms or methods disclosed, but to the contrary, the invention is to cover all modifications, equivalents and alternatives falling within the spirit and scope of the appended claims.
Claims (2)
1. An apparatus for delivering a prosthesis into a blood vessel of a patient, comprising:
an elongate tubular member having a proximal end, a distal end, and a lumen extending between the proximal and distal ends, the distal end having a size for endoluminal insertion into a blood vessel and terminating in a substantially atraumatic distal portion comprising a plurality of flexible leaflets integrally molded thereto, the leaflets being deflectable, without exposure to a softening liquid, from a closed position wherein the leaflets engage one another to an open position wherein the leaflets define an opening communicating with the lumen;
a tubular prosthesis disposed within the lumen proximate the distal portion; and
an elongate bumper member having a proximal end and a distal end, the bumper member being slidably disposed within the lumen of the elongate tubular member, the distal end of the bumper member having a blunt edge disposed adjacent the proximal end of the prosthesis for preventing axial displacement of the prosthesis upon retraction of the tubular member with respect to the bumper member;
wherein adjacent leaflets are connected to one another by weakened regions, the weakened regions being tearable upon retraction of the tubular member with respect to the prosthesis to allow the leaflets to be deflected towards the open position.
2. An apparatus for delivering a prosthesis into a blood vessel of a patient, comprising:
an elongate tubular member having a proximal end, a distal end, and a lumen extending between the proximal and distal ends, the distal end having a size for endoluminal insertion into a blood vessel and terminating in a substantially atraumatic distal portion comprising a plurality of flexible leaflets integrally molded thereto, the leaflets being deflectable, without exposure to a softening liquid, from a closed position wherein the leaflets engage one another to an open position wherein the leaflets define an opening communicating with the lumen;
a tubular prosthesis disposed within the lumen proximate the distal portion; and
an elongate bumper member having a proximal end and a distal end, the bumper member being slidably disposed within the lumen of the elongate tubular member, the distal end of the bumper member having a blunt edge disposed adjacent the proximal end of the prosthesis for preventing axial displacement of the prosthesis upon retraction of the tubular member with respect to the bumper member;
wherein the leaflets include a portion having a thickness that is substantially thinner than a wall thickness of the distal portion of the tubular member from which the leaflets extend.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/197,577 US20050283222A1 (en) | 2000-09-18 | 2005-08-03 | Apparatus for delivering endoluminal prostheses and methods of making and using them |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/664,970 US6945989B1 (en) | 2000-09-18 | 2000-09-18 | Apparatus for delivering endoluminal prostheses and methods of making and using them |
US11/197,577 US20050283222A1 (en) | 2000-09-18 | 2005-08-03 | Apparatus for delivering endoluminal prostheses and methods of making and using them |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/664,970 Continuation US6945989B1 (en) | 2000-09-18 | 2000-09-18 | Apparatus for delivering endoluminal prostheses and methods of making and using them |
Publications (1)
Publication Number | Publication Date |
---|---|
US20050283222A1 true US20050283222A1 (en) | 2005-12-22 |
Family
ID=24668180
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/664,970 Expired - Lifetime US6945989B1 (en) | 2000-09-18 | 2000-09-18 | Apparatus for delivering endoluminal prostheses and methods of making and using them |
US11/197,577 Abandoned US20050283222A1 (en) | 2000-09-18 | 2005-08-03 | Apparatus for delivering endoluminal prostheses and methods of making and using them |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/664,970 Expired - Lifetime US6945989B1 (en) | 2000-09-18 | 2000-09-18 | Apparatus for delivering endoluminal prostheses and methods of making and using them |
Country Status (8)
Country | Link |
---|---|
US (2) | US6945989B1 (en) |
EP (1) | EP1318769B1 (en) |
JP (1) | JP4874502B2 (en) |
AT (1) | ATE422860T1 (en) |
CA (1) | CA2422722C (en) |
DE (1) | DE60137698D1 (en) |
ES (1) | ES2320737T3 (en) |
WO (1) | WO2002022053A2 (en) |
Cited By (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20070066943A1 (en) * | 2005-09-21 | 2007-03-22 | Abiomed, Inc. | Cannula systems and methods of use |
US20090138065A1 (en) * | 2007-11-28 | 2009-05-28 | Wilson-Cook Medical Inc. | Double loaded stent delivery system |
US20090264978A1 (en) * | 2008-03-27 | 2009-10-22 | Dieck Martin S | Friction-Release Distal Latch Implant Delivery System and Components |
US9095343B2 (en) | 2005-05-25 | 2015-08-04 | Covidien Lp | System and method for delivering and deploying an occluding device within a vessel |
US9155647B2 (en) | 2012-07-18 | 2015-10-13 | Covidien Lp | Methods and apparatus for luminal stenting |
US9204983B2 (en) | 2005-05-25 | 2015-12-08 | Covidien Lp | System and method for delivering and deploying an occluding device within a vessel |
US9675482B2 (en) | 2008-05-13 | 2017-06-13 | Covidien Lp | Braid implant delivery systems |
CN108784897A (en) * | 2017-04-28 | 2018-11-13 | 柯惠有限合伙公司 | stent delivery system |
Families Citing this family (111)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20020193863A1 (en) * | 2000-09-18 | 2002-12-19 | Endotex Interventional Systems, Inc. | Apparatus for delivering endoluminal prosthesis and methods for preparing such apparatus for delivery |
US8075606B2 (en) | 2001-07-06 | 2011-12-13 | Angiomed Gmbh & Co. Medizintechnik Kg | Delivery system having a rapid pusher assembly for self-expanding stent, and stent exchange configuration |
GB0121980D0 (en) | 2001-09-11 | 2001-10-31 | Cathnet Science Holding As | Expandable stent |
US20030050648A1 (en) | 2001-09-11 | 2003-03-13 | Spiration, Inc. | Removable lung reduction devices, systems, and methods |
GB0123633D0 (en) | 2001-10-02 | 2001-11-21 | Angiomed Ag | Stent delivery system |
US6592594B2 (en) | 2001-10-25 | 2003-07-15 | Spiration, Inc. | Bronchial obstruction device deployment system and method |
US20050228479A1 (en) * | 2001-11-29 | 2005-10-13 | Cook Incorporated | Medical device delivery system |
DE60221289T2 (en) * | 2001-11-29 | 2008-04-10 | Cook Inc., Bloomington | FEEDING SYSTEM FOR MEDICAL DEVICES |
US7294146B2 (en) | 2001-12-03 | 2007-11-13 | Xtent, Inc. | Apparatus and methods for delivery of variable length stents |
US7892273B2 (en) | 2001-12-03 | 2011-02-22 | Xtent, Inc. | Custom length stent apparatus |
US8080048B2 (en) * | 2001-12-03 | 2011-12-20 | Xtent, Inc. | Stent delivery for bifurcated vessels |
US20040186551A1 (en) | 2003-01-17 | 2004-09-23 | Xtent, Inc. | Multiple independent nested stent structures and methods for their preparation and deployment |
US7351255B2 (en) | 2001-12-03 | 2008-04-01 | Xtent, Inc. | Stent delivery apparatus and method |
US7182779B2 (en) | 2001-12-03 | 2007-02-27 | Xtent, Inc. | Apparatus and methods for positioning prostheses for deployment from a catheter |
US20030135266A1 (en) | 2001-12-03 | 2003-07-17 | Xtent, Inc. | Apparatus and methods for delivery of multiple distributed stents |
US7147656B2 (en) | 2001-12-03 | 2006-12-12 | Xtent, Inc. | Apparatus and methods for delivery of braided prostheses |
US7309350B2 (en) | 2001-12-03 | 2007-12-18 | Xtent, Inc. | Apparatus and methods for deployment of vascular prostheses |
US7137993B2 (en) | 2001-12-03 | 2006-11-21 | Xtent, Inc. | Apparatus and methods for delivery of multiple distributed stents |
US6989024B2 (en) | 2002-02-28 | 2006-01-24 | Counter Clockwise, Inc. | Guidewire loaded stent for delivery through a catheter |
US20030181922A1 (en) | 2002-03-20 | 2003-09-25 | Spiration, Inc. | Removable anchored lung volume reduction devices and methods |
US20030216769A1 (en) | 2002-05-17 | 2003-11-20 | Dillard David H. | Removable anchored lung volume reduction devices and methods |
WO2004011050A1 (en) * | 2002-07-30 | 2004-02-05 | Nanyang Technological University | Spherical nano-composite powder and a method of preparing the same |
EP1552837A1 (en) * | 2002-08-01 | 2005-07-13 | Chugai Seiyaku Kabushiki Kaisha | Antipsoriatic agent |
US20040116997A1 (en) | 2002-09-20 | 2004-06-17 | Taylor Charles S. | Stent-graft with positioning anchor |
US7169172B2 (en) * | 2002-11-01 | 2007-01-30 | Counter Clockwise, Inc. | Method and apparatus for caged stent delivery |
US8449594B2 (en) | 2002-11-01 | 2013-05-28 | Marc-Alan Levine | Method and apparatus for caged stent delivery |
CA2513082C (en) * | 2003-01-15 | 2010-11-02 | Angiomed Gmbh & Co. Medizintechnik Kg | Trans-luminal surgical device |
US7303533B2 (en) * | 2003-04-10 | 2007-12-04 | Intraluminal Therapeutics, Inc. | Shapeable intraluminal device and method therefor |
GB0309616D0 (en) * | 2003-04-28 | 2003-06-04 | Angiomed Gmbh & Co | Loading and delivery of self-expanding stents |
CA2526276C (en) * | 2003-05-23 | 2011-05-03 | Kabushikikaisha Igaki Iryo Sekkei | Stent supplying device |
US7241308B2 (en) | 2003-06-09 | 2007-07-10 | Xtent, Inc. | Stent deployment systems and methods |
US7533671B2 (en) | 2003-08-08 | 2009-05-19 | Spiration, Inc. | Bronchoscopic repair of air leaks in a lung |
US9198786B2 (en) | 2003-09-03 | 2015-12-01 | Bolton Medical, Inc. | Lumen repair device with capture structure |
US20080264102A1 (en) | 2004-02-23 | 2008-10-30 | Bolton Medical, Inc. | Sheath Capture Device for Stent Graft Delivery System and Method for Operating Same |
US8500792B2 (en) | 2003-09-03 | 2013-08-06 | Bolton Medical, Inc. | Dual capture device for stent graft delivery system and method for capturing a stent graft |
US7763063B2 (en) | 2003-09-03 | 2010-07-27 | Bolton Medical, Inc. | Self-aligning stent graft delivery system, kit, and method |
US11596537B2 (en) | 2003-09-03 | 2023-03-07 | Bolton Medical, Inc. | Delivery system and method for self-centering a proximal end of a stent graft |
US8292943B2 (en) | 2003-09-03 | 2012-10-23 | Bolton Medical, Inc. | Stent graft with longitudinal support member |
US20070198078A1 (en) | 2003-09-03 | 2007-08-23 | Bolton Medical, Inc. | Delivery system and method for self-centering a Proximal end of a stent graft |
US11259945B2 (en) | 2003-09-03 | 2022-03-01 | Bolton Medical, Inc. | Dual capture device for stent graft delivery system and method for capturing a stent graft |
GB0322511D0 (en) * | 2003-09-25 | 2003-10-29 | Angiomed Ag | Lining for bodily lumen |
DE10346200A1 (en) * | 2003-09-30 | 2005-05-04 | Jotec Gmbh | Delivery system with a self-expanding stent |
US7326236B2 (en) | 2003-12-23 | 2008-02-05 | Xtent, Inc. | Devices and methods for controlling and indicating the length of an interventional element |
US7323006B2 (en) | 2004-03-30 | 2008-01-29 | Xtent, Inc. | Rapid exchange interventional devices and methods |
US7717951B2 (en) | 2004-05-06 | 2010-05-18 | Cook Incorporated | Delivery system that facilitates visual inspection of an intraluminal medical device |
US8317859B2 (en) | 2004-06-28 | 2012-11-27 | J.W. Medical Systems Ltd. | Devices and methods for controlling expandable prostheses during deployment |
US20050288766A1 (en) | 2004-06-28 | 2005-12-29 | Xtent, Inc. | Devices and methods for controlling expandable prostheses during deployment |
US8048145B2 (en) | 2004-07-22 | 2011-11-01 | Endologix, Inc. | Graft systems having filling structures supported by scaffolds and methods for their use |
US8109983B2 (en) * | 2004-08-06 | 2012-02-07 | Boston Scientific Scimed, Inc. | Medical device delivery systems |
US8652193B2 (en) | 2005-05-09 | 2014-02-18 | Angiomed Gmbh & Co. Medizintechnik Kg | Implant delivery device |
AU2006269419A1 (en) | 2005-07-07 | 2007-01-18 | Nellix, Inc. | Systems and methods for endovascular aneurysm treatment |
WO2007095031A2 (en) * | 2006-02-13 | 2007-08-23 | Bay Street Medical, Inc. | System for delivering a stent |
US20070208408A1 (en) * | 2006-03-06 | 2007-09-06 | Boston Scientific Scimed, Inc. | Non-foreshortening sheaths and assemblies for use |
JP2009530060A (en) | 2006-03-20 | 2009-08-27 | エックステント・インコーポレーテッド | Apparatus and method for deploying connected prosthetic segments |
US7691151B2 (en) | 2006-03-31 | 2010-04-06 | Spiration, Inc. | Articulable Anchor |
US20080199510A1 (en) | 2007-02-20 | 2008-08-21 | Xtent, Inc. | Thermo-mechanically controlled implants and methods of use |
US8486132B2 (en) | 2007-03-22 | 2013-07-16 | J.W. Medical Systems Ltd. | Devices and methods for controlling expandable prostheses during deployment |
JP5667873B2 (en) * | 2007-06-21 | 2015-02-12 | カペラ・インコーポレイテッド | Medical device delivery system with sheath having balloon relative position |
US9144508B2 (en) | 2007-07-19 | 2015-09-29 | Back Bay Medical Inc. | Radially expandable stent |
US8663309B2 (en) | 2007-09-26 | 2014-03-04 | Trivascular, Inc. | Asymmetric stent apparatus and method |
US8066755B2 (en) | 2007-09-26 | 2011-11-29 | Trivascular, Inc. | System and method of pivoted stent deployment |
US8226701B2 (en) | 2007-09-26 | 2012-07-24 | Trivascular, Inc. | Stent and delivery system for deployment thereof |
CN101917929A (en) | 2007-10-04 | 2010-12-15 | 特里瓦斯库拉尔公司 | Modular vascular graft for low profile percutaneous delivery |
EP2194933B1 (en) | 2007-10-12 | 2016-05-04 | Spiration, Inc. | Valve loader method, system, and apparatus |
US8083789B2 (en) | 2007-11-16 | 2011-12-27 | Trivascular, Inc. | Securement assembly and method for expandable endovascular device |
US8328861B2 (en) | 2007-11-16 | 2012-12-11 | Trivascular, Inc. | Delivery system and method for bifurcated graft |
US9101503B2 (en) | 2008-03-06 | 2015-08-11 | J.W. Medical Systems Ltd. | Apparatus having variable strut length and methods of use |
CA2721950A1 (en) * | 2008-04-25 | 2009-10-29 | Nellix, Inc. | Stent graft delivery system |
AU2009256084A1 (en) | 2008-06-04 | 2009-12-10 | Nellix, Inc. | Sealing apparatus and methods of use |
GB0810749D0 (en) | 2008-06-11 | 2008-07-16 | Angiomed Ag | Catherter delivery device |
US9750625B2 (en) * | 2008-06-11 | 2017-09-05 | C.R. Bard, Inc. | Catheter delivery device |
US20090319019A1 (en) * | 2008-06-23 | 2009-12-24 | Cook Incorporated | Expandable Tip Delivery System For Endoluminal Prosthesis |
CN107961098A (en) | 2008-06-30 | 2018-04-27 | 波顿医疗公司 | System and method for abdominal aneurvsm |
CN102215780B (en) | 2008-09-25 | 2015-10-14 | 高级分支系统股份有限公司 | Part crimped stent |
US8795347B2 (en) | 2008-09-25 | 2014-08-05 | Advanced Bifurcation Systems, Inc. | Methods and systems for treating a bifurcation with provisional side branch stenting |
US11298252B2 (en) | 2008-09-25 | 2022-04-12 | Advanced Bifurcation Systems Inc. | Stent alignment during treatment of a bifurcation |
US8769796B2 (en) | 2008-09-25 | 2014-07-08 | Advanced Bifurcation Systems, Inc. | Selective stent crimping |
US8821562B2 (en) | 2008-09-25 | 2014-09-02 | Advanced Bifurcation Systems, Inc. | Partially crimped stent |
GB0901496D0 (en) | 2009-01-29 | 2009-03-11 | Angiomed Ag | Delivery device for delivering a stent device |
EP3284447B1 (en) | 2009-03-13 | 2020-05-20 | Bolton Medical Inc. | System for deploying an endoluminal prosthesis at a surgical site |
GB0909319D0 (en) | 2009-05-29 | 2009-07-15 | Angiomed Ag | Transluminal delivery system |
US20110276078A1 (en) | 2009-12-30 | 2011-11-10 | Nellix, Inc. | Filling structure for a graft system and methods of use |
WO2011119883A1 (en) | 2010-03-24 | 2011-09-29 | Advanced Bifurcation Systems, Inc. | Stent alignment during treatment of a bifurcation |
CA2794080A1 (en) | 2010-03-24 | 2011-09-29 | Advanced Bifurcation Systems, Inc. | System and methods for treating a bifurcation |
US8801768B2 (en) | 2011-01-21 | 2014-08-12 | Endologix, Inc. | Graft systems having semi-permeable filling structures and methods for their use |
EP2672932B1 (en) | 2011-02-08 | 2018-09-19 | Advanced Bifurcation Systems, Inc. | System for treating a bifurcation with a fully crimped stent |
WO2012109382A2 (en) | 2011-02-08 | 2012-08-16 | Advanced Bifurcation Systems, Inc. | Multi-stent and multi-balloon apparatus for treating bifurcations and methods of use |
JP5976777B2 (en) | 2011-04-06 | 2016-08-24 | エンドーロジックス インコーポレイテッド | Methods and systems for the treatment of intravascular aneurysms |
US8795241B2 (en) | 2011-05-13 | 2014-08-05 | Spiration, Inc. | Deployment catheter |
US9724223B2 (en) | 2011-05-27 | 2017-08-08 | Abbotcardiovascular Systems Inc. | Delivery system for a self expanding stent |
RU2502482C2 (en) * | 2011-12-19 | 2013-12-27 | Федеральное государственное автономное образовательное учреждение высшего профессионального образования "Национальный исследовательский технологический университет "МИСиС" | Method of surgical treatment of intestinal obstruction of small and large intestine and device for its realisation |
US10940167B2 (en) | 2012-02-10 | 2021-03-09 | Cvdevices, Llc | Methods and uses of biological tissues for various stent and other medical applications |
US8992595B2 (en) | 2012-04-04 | 2015-03-31 | Trivascular, Inc. | Durable stent graft with tapered struts and stable delivery methods and devices |
US9498363B2 (en) | 2012-04-06 | 2016-11-22 | Trivascular, Inc. | Delivery catheter for endovascular device |
WO2013154749A1 (en) | 2012-04-12 | 2013-10-17 | Bolton Medical, Inc. | Vascular prosthetic delivery device and method of use |
US9271855B2 (en) | 2012-05-09 | 2016-03-01 | Abbott Cardiovascular Systems Inc. | Catheter having hydraulic actuator with tandem chambers |
US9011513B2 (en) | 2012-05-09 | 2015-04-21 | Abbott Cardiovascular Systems Inc. | Catheter having hydraulic actuator |
US20130304180A1 (en) | 2012-05-09 | 2013-11-14 | Michael L. Green | Catheter having dual balloon hydraulic actuator |
US9233015B2 (en) | 2012-06-15 | 2016-01-12 | Trivascular, Inc. | Endovascular delivery system with an improved radiopaque marker scheme |
AU2014214700B2 (en) | 2013-02-11 | 2018-01-18 | Cook Medical Technologies Llc | Expandable support frame and medical device |
US10420662B2 (en) | 2013-03-12 | 2019-09-24 | Abbott Cardiovascular Systems Inc. | Catheter having movable tubular structure and proximal stopper |
US10531971B2 (en) | 2013-03-12 | 2020-01-14 | Abbott Cardiovascular System Inc. | Balloon catheter having hydraulic actuator |
US9283101B2 (en) | 2013-03-12 | 2016-03-15 | Abbott Cardiovascular Systems Inc. | Catheter having hydraulic actuator and locking system |
US9326875B2 (en) * | 2013-03-13 | 2016-05-03 | Abbott Cardiovascular Systems Inc. | Catheter having a movable tubular structure and method of making |
GB2526034B (en) | 2013-03-14 | 2020-03-04 | Spiration Inc | Valve loader method, system and apparatus |
US9289536B2 (en) | 2013-03-14 | 2016-03-22 | Endologix, Inc. | Method for forming materials in situ within a medical device |
US9439751B2 (en) | 2013-03-15 | 2016-09-13 | Bolton Medical, Inc. | Hemostasis valve and delivery systems |
US10315007B2 (en) * | 2014-07-15 | 2019-06-11 | Stryker Corporation | Vascular access system and method of use |
US20160120678A1 (en) | 2014-11-04 | 2016-05-05 | Abbott Cardiovascular Systems Inc. | Methods and systems for delivering an implant |
US10639181B2 (en) | 2014-11-04 | 2020-05-05 | Abbott Cardiovascular Systems Inc. | Methods and systems for delivering an implant |
EP4281012A1 (en) * | 2021-01-19 | 2023-11-29 | Edwards Lifesciences Corporation | Delivery apparatus and methods for prosthetic valve docking devices |
Citations (93)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3204635A (en) * | 1963-03-21 | 1965-09-07 | Voss | Hygienic devices |
US3485234A (en) * | 1966-04-13 | 1969-12-23 | Cordis Corp | Tubular products and method of making same |
US3585707A (en) * | 1966-04-13 | 1971-06-22 | Cordis Corp | Method of making tubular products |
US3760808A (en) * | 1969-12-01 | 1973-09-25 | K Bleuer | Tampon applicator assembly |
US4023559A (en) * | 1975-01-28 | 1977-05-17 | Smith & Nephew (Australia) Pty. Limited | Sampling catheter device |
US4157709A (en) * | 1977-05-09 | 1979-06-12 | Ovutime, Inc. | Probe for obtaining cervical mucus and process thereof |
US4356610A (en) * | 1978-04-17 | 1982-11-02 | American Home Products Corporation | Method of manufacturing catheter for measuring intrauterine pressure or the like |
US4424054A (en) * | 1978-05-17 | 1984-01-03 | Kcdp Corporation | Fluid-expansible contraceptive tampon and applicator |
US4516972A (en) * | 1982-01-28 | 1985-05-14 | Advanced Cardiovascular Systems, Inc. | Guiding catheter and method of manufacture |
US4681110A (en) * | 1985-12-02 | 1987-07-21 | Wiktor Dominik M | Catheter arrangement having a blood vessel liner, and method of using it |
US4710181A (en) * | 1985-06-11 | 1987-12-01 | Genus Catheter Technologies, Inc. | Variable diameter catheter |
US4738666A (en) * | 1985-06-11 | 1988-04-19 | Genus Catheter Technologies, Inc. | Variable diameter catheter |
US4739762A (en) * | 1985-11-07 | 1988-04-26 | Expandable Grafts Partnership | Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft |
US4817613A (en) * | 1987-07-13 | 1989-04-04 | Devices For Vascular Intervention, Inc. | Guiding catheter |
US4842590A (en) * | 1983-12-14 | 1989-06-27 | Terumo Kabushiki Kaisha | Catheter and method for making |
US4848343A (en) * | 1986-10-31 | 1989-07-18 | Medinvent S.A. | Device for transluminal implantation |
US5019090A (en) * | 1988-09-01 | 1991-05-28 | Corvita Corporation | Radially expandable endoprosthesis and the like |
US5037329A (en) * | 1990-09-27 | 1991-08-06 | Gte Products Corporation | Angular connector for a shielded coaxial cable |
US5041126A (en) * | 1987-03-13 | 1991-08-20 | Cook Incorporated | Endovascular stent and delivery system |
US5057092A (en) * | 1990-04-04 | 1991-10-15 | Webster Wilton W Jr | Braided catheter with low modulus warp |
US5089006A (en) * | 1989-11-29 | 1992-02-18 | Stiles Frank B | Biological duct liner and installation catheter |
US5104399A (en) * | 1986-12-10 | 1992-04-14 | Endovascular Technologies, Inc. | Artificial graft and implantation method |
US5129402A (en) * | 1991-02-19 | 1992-07-14 | Accu-Med Corporation | Apparatus for collecting and/or growing protected biological specimens |
US5147385A (en) * | 1989-11-01 | 1992-09-15 | Schneider (Europe) A.G. | Stent and catheter for the introduction of the stent |
US5158548A (en) * | 1990-04-25 | 1992-10-27 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5192297A (en) * | 1991-12-31 | 1993-03-09 | Medtronic, Inc. | Apparatus and method for placement and implantation of a stent |
US5201901A (en) * | 1987-10-08 | 1993-04-13 | Terumo Kabushiki Kaisha | Expansion unit and apparatus for expanding tubular organ lumen |
US5242399A (en) * | 1990-04-25 | 1993-09-07 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5246421A (en) * | 1992-02-12 | 1993-09-21 | Saab Mark A | Method of treating obstructed regions of bodily passages |
US5254107A (en) * | 1991-03-06 | 1993-10-19 | Cordis Corporation | Catheter having extended braid reinforced transitional tip |
US5279596A (en) * | 1990-07-27 | 1994-01-18 | Cordis Corporation | Intravascular catheter with kink resistant tip |
US5290310A (en) * | 1991-10-30 | 1994-03-01 | Howmedica, Inc. | Hemostatic implant introducer |
US5290295A (en) * | 1992-07-15 | 1994-03-01 | Querals & Fine, Inc. | Insertion tool for an intraluminal graft procedure |
US5312415A (en) * | 1992-09-22 | 1994-05-17 | Target Therapeutics, Inc. | Assembly for placement of embolic coils using frictional placement |
US5354302A (en) * | 1992-11-06 | 1994-10-11 | Ko Sung Tao | Medical device and method for facilitating intra-tissue visual observation and manipulation of distensible tissues |
US5360401A (en) * | 1993-02-18 | 1994-11-01 | Advanced Cardiovascular Systems, Inc. | Catheter for stent delivery |
US5389067A (en) * | 1992-05-20 | 1995-02-14 | Playtex Family Products Corporation | Tampon applicator and method of making same |
US5391172A (en) * | 1993-05-24 | 1995-02-21 | Advanced Cardiovascular Systems, Inc. | Stent delivery system with coaxial catheter handle |
US5395308A (en) * | 1993-09-24 | 1995-03-07 | Kimberly-Clark Corporation | Thermoplastic applicator exhibiting accelerated breakup when immersed in water |
US5433723A (en) * | 1991-10-11 | 1995-07-18 | Angiomed Ag | Apparatus for widening a stenosis |
US5443457A (en) * | 1994-02-24 | 1995-08-22 | Cardiovascular Imaging Systems, Incorporated | Tracking tip for a short lumen rapid exchange catheter |
US5453090A (en) * | 1994-03-01 | 1995-09-26 | Cordis Corporation | Method of stent delivery through an elongate softenable sheath |
US5458625A (en) * | 1994-05-04 | 1995-10-17 | Kendall; Donald E. | Transcutaneous nerve stimulation device and method for using same |
US5458605A (en) * | 1994-04-04 | 1995-10-17 | Advanced Cardiovascular Systems, Inc. | Coiled reinforced retractable sleeve for stent delivery catheter |
US5460608A (en) * | 1994-01-25 | 1995-10-24 | Scimed Life Systems, Inc. | Kink free catheter |
US5484425A (en) * | 1990-05-01 | 1996-01-16 | Cathco, Inc. | Radiopaque non-kinking thin-walled introducer sheath |
US5484444A (en) * | 1992-10-31 | 1996-01-16 | Schneider (Europe) A.G. | Device for the implantation of self-expanding endoprostheses |
US5534007A (en) * | 1995-05-18 | 1996-07-09 | Scimed Life Systems, Inc. | Stent deployment catheter with collapsible sheath |
US5549635A (en) * | 1994-01-24 | 1996-08-27 | Solar, Rita & Gaterud, Ltd. | Non-deformable self-expanding parallel flow endovascular stent and deployment apparatus therefore |
US5554139A (en) * | 1993-12-24 | 1996-09-10 | Terumo Kabushiki Kaisha | Catheter |
US5554118A (en) * | 1991-05-24 | 1996-09-10 | Jang; G. David | Universal mode vascular catheter system |
US5601568A (en) * | 1994-04-11 | 1997-02-11 | B. Braun Celsa (Societe Anonyme) | Handle for the controlled relative sliding of a sheath and of a stem; apparatus comprising such a handle and method for implanting a blood filter using a handle |
US5630801A (en) * | 1993-10-05 | 1997-05-20 | B. Braun Celsa | Device for implanting a medical prosthesis in a duct of a human or animal body |
US5662703A (en) * | 1995-04-14 | 1997-09-02 | Schneider (Usa) Inc. | Rolling membrane stent delivery device |
US5669936A (en) * | 1983-12-09 | 1997-09-23 | Endovascular Technologies, Inc. | Endovascular grafting system and method for use therewith |
US5674208A (en) * | 1993-08-18 | 1997-10-07 | Scimed Life Systems, Inc. | Thin-walled catheter |
US5683451A (en) * | 1994-06-08 | 1997-11-04 | Cardiovascular Concepts, Inc. | Apparatus and methods for deployment release of intraluminal prostheses |
US5690644A (en) * | 1992-12-30 | 1997-11-25 | Schneider (Usa) Inc. | Apparatus for deploying body implantable stent |
US5693086A (en) * | 1994-02-09 | 1997-12-02 | Boston Scientific Technology, Inc. | Apparatus for delivering an endoluminal stent or prosthesis |
US5704926A (en) * | 1994-11-23 | 1998-01-06 | Navarre Biomedical, Ltd. | Flexible catheter |
US5707376A (en) * | 1992-08-06 | 1998-01-13 | William Cook Europe A/S | Stent introducer and method of use |
US5709703A (en) * | 1995-11-14 | 1998-01-20 | Schneider (Europe) A.G. | Stent delivery device and method for manufacturing same |
US5735859A (en) * | 1997-02-14 | 1998-04-07 | Cathco, Inc. | Distally attachable and releasable sheath for a stent delivery system |
US5743874A (en) * | 1994-08-29 | 1998-04-28 | Fischell; Robert E. | Integrated catheter for balloon angioplasty and stent delivery |
US5752970A (en) * | 1995-02-03 | 1998-05-19 | Yoon; Inbae | Cannula with distal end valve |
US5759186A (en) * | 1991-06-14 | 1998-06-02 | Ams Medinvent S.A. | Transluminal Implantation device |
US5772669A (en) * | 1996-09-27 | 1998-06-30 | Scimed Life Systems, Inc. | Stent deployment catheter with retractable sheath |
US5782855A (en) * | 1991-01-28 | 1998-07-21 | Advanced Cardiovascular Systems, Inc. | Stent delivery system |
US5788707A (en) * | 1995-06-07 | 1998-08-04 | Scimed Life Systems, Inc. | Pull back sleeve system with compression resistant inner shaft |
US5800517A (en) * | 1996-08-19 | 1998-09-01 | Scimed Life Systems, Inc. | Stent delivery system with storage sleeve |
US5814062A (en) * | 1994-12-22 | 1998-09-29 | Target Therapeutics, Inc. | Implant delivery assembly with expandable coupling/decoupling mechanism |
US5817100A (en) * | 1994-02-07 | 1998-10-06 | Kabushikikaisya Igaki Iryo Sekkei | Stent device and stent supplying system |
US5824041A (en) * | 1994-06-08 | 1998-10-20 | Medtronic, Inc. | Apparatus and methods for placement and repositioning of intraluminal prostheses |
US5833694A (en) * | 1995-05-25 | 1998-11-10 | Medtronic, Inc. | Stent assembly and method of use |
US5868707A (en) * | 1996-08-15 | 1999-02-09 | Advanced Cardiovascular Systems, Inc. | Protective sheath for catheter balloons |
US5868755A (en) * | 1997-01-16 | 1999-02-09 | Atrion Medical Products, Inc. | Sheath retractor mechanism and method |
US5891090A (en) * | 1994-03-14 | 1999-04-06 | Advanced Cardiovascular Systems, Inc. | Perfusion dilatation catheter with expanded support coil |
US5906619A (en) * | 1997-07-24 | 1999-05-25 | Medtronic, Inc. | Disposable delivery device for endoluminal prostheses |
US5928183A (en) * | 1994-08-22 | 1999-07-27 | Kimberly-Clark Worldwide, Inc. | Tampon applicator with multi-layered tips |
US5935135A (en) * | 1995-09-29 | 1999-08-10 | United States Surgical Corporation | Balloon delivery system for deploying stents |
US5957974A (en) * | 1997-01-23 | 1999-09-28 | Schneider (Usa) Inc | Stent graft with braided polymeric sleeve |
US6013019A (en) * | 1998-04-06 | 2000-01-11 | Isostent, Inc. | Temporary radioisotope stent |
US6019778A (en) * | 1998-03-13 | 2000-02-01 | Cordis Corporation | Delivery apparatus for a self-expanding stent |
US6063112A (en) * | 1995-12-28 | 2000-05-16 | Sofradim Production | Kit for surgical treatment of intracorporeal lumens |
US6063111A (en) * | 1998-03-31 | 2000-05-16 | Cordis Corporation | Stent aneurysm treatment system and method |
US6077295A (en) * | 1996-07-15 | 2000-06-20 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent delivery system |
US6146415A (en) * | 1999-05-07 | 2000-11-14 | Advanced Cardiovascular Systems, Inc. | Stent delivery system |
US6193686B1 (en) * | 1999-06-30 | 2001-02-27 | Advanced Cardiovascular Systems, Inc. | Catheter with enhanced flexibility |
US6241758B1 (en) * | 1999-05-28 | 2001-06-05 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent delivery system and method of use |
US20010044648A1 (en) * | 1998-02-05 | 2001-11-22 | Medtronic, Inc. | Radially-expandable stent and delivery system |
US6517558B2 (en) * | 1999-01-15 | 2003-02-11 | Ventrica, Inc. | Methods and devices for forming vascular anastomoses |
US6607551B1 (en) * | 1999-05-20 | 2003-08-19 | Scimed Life Systems, Inc. | Stent delivery system with nested stabilizer |
US6676693B1 (en) * | 2001-06-27 | 2004-01-13 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for delivering a self-expanding stent |
Family Cites Families (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5104339A (en) | 1989-10-11 | 1992-04-14 | E. I. Du Pont De Nemours And Company | Electrical circuit component with latching means for mounting to a circuit substrate |
US5306294A (en) | 1992-08-05 | 1994-04-26 | Ultrasonic Sensing And Monitoring Systems, Inc. | Stent construction of rolled configuration |
US5443400A (en) | 1993-10-18 | 1995-08-22 | Heyco Stamped Products, Inc. | Multiple outlet receptacle and metal stamping therefor |
US5456694A (en) | 1994-05-13 | 1995-10-10 | Stentco, Inc. | Device for delivering and deploying intraluminal devices |
WO1996013228A1 (en) | 1994-10-27 | 1996-05-09 | Schneider (Usa) Inc. | Stent delivery device |
US5700269A (en) | 1995-06-06 | 1997-12-23 | Corvita Corporation | Endoluminal prosthesis deployment device for use with prostheses of variable length and having retraction ability |
US5702418A (en) | 1995-09-12 | 1997-12-30 | Boston Scientific Corporation | Stent delivery system |
US6743219B1 (en) * | 2000-08-02 | 2004-06-01 | Cordis Corporation | Delivery apparatus for a self-expanding stent |
-
2000
- 2000-09-18 US US09/664,970 patent/US6945989B1/en not_active Expired - Lifetime
-
2001
- 2001-09-17 AT AT01971160T patent/ATE422860T1/en not_active IP Right Cessation
- 2001-09-17 JP JP2002526308A patent/JP4874502B2/en not_active Expired - Fee Related
- 2001-09-17 ES ES01971160T patent/ES2320737T3/en not_active Expired - Lifetime
- 2001-09-17 EP EP01971160A patent/EP1318769B1/en not_active Expired - Lifetime
- 2001-09-17 DE DE60137698T patent/DE60137698D1/en not_active Expired - Lifetime
- 2001-09-17 WO PCT/US2001/029166 patent/WO2002022053A2/en active Application Filing
- 2001-09-17 CA CA002422722A patent/CA2422722C/en not_active Expired - Fee Related
-
2005
- 2005-08-03 US US11/197,577 patent/US20050283222A1/en not_active Abandoned
Patent Citations (100)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3204635A (en) * | 1963-03-21 | 1965-09-07 | Voss | Hygienic devices |
US3485234A (en) * | 1966-04-13 | 1969-12-23 | Cordis Corp | Tubular products and method of making same |
US3585707A (en) * | 1966-04-13 | 1971-06-22 | Cordis Corp | Method of making tubular products |
US3760808A (en) * | 1969-12-01 | 1973-09-25 | K Bleuer | Tampon applicator assembly |
US4023559A (en) * | 1975-01-28 | 1977-05-17 | Smith & Nephew (Australia) Pty. Limited | Sampling catheter device |
US4157709A (en) * | 1977-05-09 | 1979-06-12 | Ovutime, Inc. | Probe for obtaining cervical mucus and process thereof |
US4356610A (en) * | 1978-04-17 | 1982-11-02 | American Home Products Corporation | Method of manufacturing catheter for measuring intrauterine pressure or the like |
US4424054A (en) * | 1978-05-17 | 1984-01-03 | Kcdp Corporation | Fluid-expansible contraceptive tampon and applicator |
US4516972A (en) * | 1982-01-28 | 1985-05-14 | Advanced Cardiovascular Systems, Inc. | Guiding catheter and method of manufacture |
US5669936A (en) * | 1983-12-09 | 1997-09-23 | Endovascular Technologies, Inc. | Endovascular grafting system and method for use therewith |
US4842590A (en) * | 1983-12-14 | 1989-06-27 | Terumo Kabushiki Kaisha | Catheter and method for making |
US4710181A (en) * | 1985-06-11 | 1987-12-01 | Genus Catheter Technologies, Inc. | Variable diameter catheter |
US4738666A (en) * | 1985-06-11 | 1988-04-19 | Genus Catheter Technologies, Inc. | Variable diameter catheter |
US4739762A (en) * | 1985-11-07 | 1988-04-26 | Expandable Grafts Partnership | Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft |
US4739762B1 (en) * | 1985-11-07 | 1998-10-27 | Expandable Grafts Partnership | Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft |
US4681110A (en) * | 1985-12-02 | 1987-07-21 | Wiktor Dominik M | Catheter arrangement having a blood vessel liner, and method of using it |
US4848343A (en) * | 1986-10-31 | 1989-07-18 | Medinvent S.A. | Device for transluminal implantation |
US5104399A (en) * | 1986-12-10 | 1992-04-14 | Endovascular Technologies, Inc. | Artificial graft and implantation method |
US5041126A (en) * | 1987-03-13 | 1991-08-20 | Cook Incorporated | Endovascular stent and delivery system |
US4817613A (en) * | 1987-07-13 | 1989-04-04 | Devices For Vascular Intervention, Inc. | Guiding catheter |
US5201901A (en) * | 1987-10-08 | 1993-04-13 | Terumo Kabushiki Kaisha | Expansion unit and apparatus for expanding tubular organ lumen |
US5019090A (en) * | 1988-09-01 | 1991-05-28 | Corvita Corporation | Radially expandable endoprosthesis and the like |
US5147385A (en) * | 1989-11-01 | 1992-09-15 | Schneider (Europe) A.G. | Stent and catheter for the introduction of the stent |
US5089006A (en) * | 1989-11-29 | 1992-02-18 | Stiles Frank B | Biological duct liner and installation catheter |
US5057092A (en) * | 1990-04-04 | 1991-10-15 | Webster Wilton W Jr | Braided catheter with low modulus warp |
US5242399A (en) * | 1990-04-25 | 1993-09-07 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5158548A (en) * | 1990-04-25 | 1992-10-27 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5484425A (en) * | 1990-05-01 | 1996-01-16 | Cathco, Inc. | Radiopaque non-kinking thin-walled introducer sheath |
US5279596A (en) * | 1990-07-27 | 1994-01-18 | Cordis Corporation | Intravascular catheter with kink resistant tip |
US5037329A (en) * | 1990-09-27 | 1991-08-06 | Gte Products Corporation | Angular connector for a shielded coaxial cable |
US5782855A (en) * | 1991-01-28 | 1998-07-21 | Advanced Cardiovascular Systems, Inc. | Stent delivery system |
US5129402A (en) * | 1991-02-19 | 1992-07-14 | Accu-Med Corporation | Apparatus for collecting and/or growing protected biological specimens |
US5254107A (en) * | 1991-03-06 | 1993-10-19 | Cordis Corporation | Catheter having extended braid reinforced transitional tip |
US5554118A (en) * | 1991-05-24 | 1996-09-10 | Jang; G. David | Universal mode vascular catheter system |
US5759186A (en) * | 1991-06-14 | 1998-06-02 | Ams Medinvent S.A. | Transluminal Implantation device |
US5433723A (en) * | 1991-10-11 | 1995-07-18 | Angiomed Ag | Apparatus for widening a stenosis |
US5290310A (en) * | 1991-10-30 | 1994-03-01 | Howmedica, Inc. | Hemostatic implant introducer |
US5192297A (en) * | 1991-12-31 | 1993-03-09 | Medtronic, Inc. | Apparatus and method for placement and implantation of a stent |
US5246421A (en) * | 1992-02-12 | 1993-09-21 | Saab Mark A | Method of treating obstructed regions of bodily passages |
US5389067A (en) * | 1992-05-20 | 1995-02-14 | Playtex Family Products Corporation | Tampon applicator and method of making same |
US6024716A (en) * | 1992-05-20 | 2000-02-15 | Playtex Products, Inc. | Tampon applicator and method of forming same |
US5290295A (en) * | 1992-07-15 | 1994-03-01 | Querals & Fine, Inc. | Insertion tool for an intraluminal graft procedure |
US5707376A (en) * | 1992-08-06 | 1998-01-13 | William Cook Europe A/S | Stent introducer and method of use |
US5312415A (en) * | 1992-09-22 | 1994-05-17 | Target Therapeutics, Inc. | Assembly for placement of embolic coils using frictional placement |
US5484444A (en) * | 1992-10-31 | 1996-01-16 | Schneider (Europe) A.G. | Device for the implantation of self-expanding endoprostheses |
US5354302A (en) * | 1992-11-06 | 1994-10-11 | Ko Sung Tao | Medical device and method for facilitating intra-tissue visual observation and manipulation of distensible tissues |
US5690644A (en) * | 1992-12-30 | 1997-11-25 | Schneider (Usa) Inc. | Apparatus for deploying body implantable stent |
US5360401A (en) * | 1993-02-18 | 1994-11-01 | Advanced Cardiovascular Systems, Inc. | Catheter for stent delivery |
US5391172A (en) * | 1993-05-24 | 1995-02-21 | Advanced Cardiovascular Systems, Inc. | Stent delivery system with coaxial catheter handle |
US5674208A (en) * | 1993-08-18 | 1997-10-07 | Scimed Life Systems, Inc. | Thin-walled catheter |
US5395308A (en) * | 1993-09-24 | 1995-03-07 | Kimberly-Clark Corporation | Thermoplastic applicator exhibiting accelerated breakup when immersed in water |
US5630801A (en) * | 1993-10-05 | 1997-05-20 | B. Braun Celsa | Device for implanting a medical prosthesis in a duct of a human or animal body |
US5554139A (en) * | 1993-12-24 | 1996-09-10 | Terumo Kabushiki Kaisha | Catheter |
US5549635A (en) * | 1994-01-24 | 1996-08-27 | Solar, Rita & Gaterud, Ltd. | Non-deformable self-expanding parallel flow endovascular stent and deployment apparatus therefore |
US5460608A (en) * | 1994-01-25 | 1995-10-24 | Scimed Life Systems, Inc. | Kink free catheter |
US5817100A (en) * | 1994-02-07 | 1998-10-06 | Kabushikikaisya Igaki Iryo Sekkei | Stent device and stent supplying system |
US5693086A (en) * | 1994-02-09 | 1997-12-02 | Boston Scientific Technology, Inc. | Apparatus for delivering an endoluminal stent or prosthesis |
US5443457A (en) * | 1994-02-24 | 1995-08-22 | Cardiovascular Imaging Systems, Incorporated | Tracking tip for a short lumen rapid exchange catheter |
US5593412A (en) * | 1994-03-01 | 1997-01-14 | Cordis Corporation | Stent delivery method and apparatus |
US5453090A (en) * | 1994-03-01 | 1995-09-26 | Cordis Corporation | Method of stent delivery through an elongate softenable sheath |
US5891090A (en) * | 1994-03-14 | 1999-04-06 | Advanced Cardiovascular Systems, Inc. | Perfusion dilatation catheter with expanded support coil |
US5458605A (en) * | 1994-04-04 | 1995-10-17 | Advanced Cardiovascular Systems, Inc. | Coiled reinforced retractable sleeve for stent delivery catheter |
US5601568A (en) * | 1994-04-11 | 1997-02-11 | B. Braun Celsa (Societe Anonyme) | Handle for the controlled relative sliding of a sheath and of a stem; apparatus comprising such a handle and method for implanting a blood filter using a handle |
US5458625A (en) * | 1994-05-04 | 1995-10-17 | Kendall; Donald E. | Transcutaneous nerve stimulation device and method for using same |
US6024763A (en) * | 1994-06-08 | 2000-02-15 | Medtronic, Inc. | Apparatus and methods for deployment release of intraluminal prostheses |
US5683451A (en) * | 1994-06-08 | 1997-11-04 | Cardiovascular Concepts, Inc. | Apparatus and methods for deployment release of intraluminal prostheses |
US5824041A (en) * | 1994-06-08 | 1998-10-20 | Medtronic, Inc. | Apparatus and methods for placement and repositioning of intraluminal prostheses |
US5928183A (en) * | 1994-08-22 | 1999-07-27 | Kimberly-Clark Worldwide, Inc. | Tampon applicator with multi-layered tips |
US5743874A (en) * | 1994-08-29 | 1998-04-28 | Fischell; Robert E. | Integrated catheter for balloon angioplasty and stent delivery |
US5704926A (en) * | 1994-11-23 | 1998-01-06 | Navarre Biomedical, Ltd. | Flexible catheter |
US5814062A (en) * | 1994-12-22 | 1998-09-29 | Target Therapeutics, Inc. | Implant delivery assembly with expandable coupling/decoupling mechanism |
US5752970A (en) * | 1995-02-03 | 1998-05-19 | Yoon; Inbae | Cannula with distal end valve |
US5662703A (en) * | 1995-04-14 | 1997-09-02 | Schneider (Usa) Inc. | Rolling membrane stent delivery device |
US5534007A (en) * | 1995-05-18 | 1996-07-09 | Scimed Life Systems, Inc. | Stent deployment catheter with collapsible sheath |
US5833694A (en) * | 1995-05-25 | 1998-11-10 | Medtronic, Inc. | Stent assembly and method of use |
US5788707A (en) * | 1995-06-07 | 1998-08-04 | Scimed Life Systems, Inc. | Pull back sleeve system with compression resistant inner shaft |
US5935135A (en) * | 1995-09-29 | 1999-08-10 | United States Surgical Corporation | Balloon delivery system for deploying stents |
US5709703A (en) * | 1995-11-14 | 1998-01-20 | Schneider (Europe) A.G. | Stent delivery device and method for manufacturing same |
US6063112A (en) * | 1995-12-28 | 2000-05-16 | Sofradim Production | Kit for surgical treatment of intracorporeal lumens |
US6077295A (en) * | 1996-07-15 | 2000-06-20 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent delivery system |
US5868707A (en) * | 1996-08-15 | 1999-02-09 | Advanced Cardiovascular Systems, Inc. | Protective sheath for catheter balloons |
US5873880A (en) * | 1996-08-15 | 1999-02-23 | Advanced Cardiovascular Systems, Inc. | Protective sheath for catheter balloons |
US5964730A (en) * | 1996-08-15 | 1999-10-12 | Advanced Cardiovascular Systems, Inc. | Protective sheath for catheter balloons |
US5800517A (en) * | 1996-08-19 | 1998-09-01 | Scimed Life Systems, Inc. | Stent delivery system with storage sleeve |
US5772669A (en) * | 1996-09-27 | 1998-06-30 | Scimed Life Systems, Inc. | Stent deployment catheter with retractable sheath |
US5868755A (en) * | 1997-01-16 | 1999-02-09 | Atrion Medical Products, Inc. | Sheath retractor mechanism and method |
US5957974A (en) * | 1997-01-23 | 1999-09-28 | Schneider (Usa) Inc | Stent graft with braided polymeric sleeve |
US5735859A (en) * | 1997-02-14 | 1998-04-07 | Cathco, Inc. | Distally attachable and releasable sheath for a stent delivery system |
US5906619A (en) * | 1997-07-24 | 1999-05-25 | Medtronic, Inc. | Disposable delivery device for endoluminal prostheses |
US20010044648A1 (en) * | 1998-02-05 | 2001-11-22 | Medtronic, Inc. | Radially-expandable stent and delivery system |
US6533807B2 (en) * | 1998-02-05 | 2003-03-18 | Medtronic, Inc. | Radially-expandable stent and delivery system |
US6019778A (en) * | 1998-03-13 | 2000-02-01 | Cordis Corporation | Delivery apparatus for a self-expanding stent |
US6063111A (en) * | 1998-03-31 | 2000-05-16 | Cordis Corporation | Stent aneurysm treatment system and method |
US6013019A (en) * | 1998-04-06 | 2000-01-11 | Isostent, Inc. | Temporary radioisotope stent |
US6517558B2 (en) * | 1999-01-15 | 2003-02-11 | Ventrica, Inc. | Methods and devices for forming vascular anastomoses |
US6146415A (en) * | 1999-05-07 | 2000-11-14 | Advanced Cardiovascular Systems, Inc. | Stent delivery system |
US6607551B1 (en) * | 1999-05-20 | 2003-08-19 | Scimed Life Systems, Inc. | Stent delivery system with nested stabilizer |
US6241758B1 (en) * | 1999-05-28 | 2001-06-05 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent delivery system and method of use |
US6193686B1 (en) * | 1999-06-30 | 2001-02-27 | Advanced Cardiovascular Systems, Inc. | Catheter with enhanced flexibility |
US6676693B1 (en) * | 2001-06-27 | 2004-01-13 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for delivering a self-expanding stent |
Cited By (16)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9204983B2 (en) | 2005-05-25 | 2015-12-08 | Covidien Lp | System and method for delivering and deploying an occluding device within a vessel |
US9095343B2 (en) | 2005-05-25 | 2015-08-04 | Covidien Lp | System and method for delivering and deploying an occluding device within a vessel |
US9198666B2 (en) | 2005-05-25 | 2015-12-01 | Covidien Lp | System and method for delivering and deploying an occluding device within a vessel |
US10322018B2 (en) | 2005-05-25 | 2019-06-18 | Covidien Lp | System and method for delivering and deploying an occluding device within a vessel |
US9381104B2 (en) | 2005-05-25 | 2016-07-05 | Covidien Lp | System and method for delivering and deploying an occluding device within a vessel |
US10064747B2 (en) | 2005-05-25 | 2018-09-04 | Covidien Lp | System and method for delivering and deploying an occluding device within a vessel |
US20070066943A1 (en) * | 2005-09-21 | 2007-03-22 | Abiomed, Inc. | Cannula systems and methods of use |
US9283314B2 (en) * | 2005-09-21 | 2016-03-15 | Abiomed, Inc. | Cannula systems |
US20090138065A1 (en) * | 2007-11-28 | 2009-05-28 | Wilson-Cook Medical Inc. | Double loaded stent delivery system |
US20090264978A1 (en) * | 2008-03-27 | 2009-10-22 | Dieck Martin S | Friction-Release Distal Latch Implant Delivery System and Components |
US9675482B2 (en) | 2008-05-13 | 2017-06-13 | Covidien Lp | Braid implant delivery systems |
US11707371B2 (en) | 2008-05-13 | 2023-07-25 | Covidien Lp | Braid implant delivery systems |
US10610389B2 (en) | 2008-05-13 | 2020-04-07 | Covidien Lp | Braid implant delivery systems |
US9155647B2 (en) | 2012-07-18 | 2015-10-13 | Covidien Lp | Methods and apparatus for luminal stenting |
US9877856B2 (en) | 2012-07-18 | 2018-01-30 | Covidien Lp | Methods and apparatus for luminal stenting |
CN108784897A (en) * | 2017-04-28 | 2018-11-13 | 柯惠有限合伙公司 | stent delivery system |
Also Published As
Publication number | Publication date |
---|---|
WO2002022053A2 (en) | 2002-03-21 |
JP2004508135A (en) | 2004-03-18 |
ES2320737T3 (en) | 2009-05-28 |
CA2422722C (en) | 2010-03-09 |
DE60137698D1 (en) | 2009-04-02 |
WO2002022053A3 (en) | 2002-12-27 |
EP1318769B1 (en) | 2009-02-18 |
JP4874502B2 (en) | 2012-02-15 |
US6945989B1 (en) | 2005-09-20 |
EP1318769A2 (en) | 2003-06-18 |
CA2422722A1 (en) | 2002-03-21 |
ATE422860T1 (en) | 2009-03-15 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6945989B1 (en) | Apparatus for delivering endoluminal prostheses and methods of making and using them | |
US20020193863A1 (en) | Apparatus for delivering endoluminal prosthesis and methods for preparing such apparatus for delivery | |
US6077295A (en) | Self-expanding stent delivery system | |
US10369033B2 (en) | Delivery system and method of use for deployment of self-expandable vascular device | |
AU766325B2 (en) | Stent delivery system for prevention of kinking, and method of loading and using same | |
US6994721B2 (en) | Stent assembly | |
EP1129674B1 (en) | Stent delivery system having delivery catheter member with a clear transition zone | |
US20110125248A1 (en) | Custom length stent apparatus | |
US20070021828A1 (en) | Mechanically actuated stents and apparatus and methods for delivering them | |
JP2002102356A (en) | A delivery apparatus for self-expanding stent | |
WO2001035715A2 (en) | Method for placing bifurcated stents | |
JP2011528572A (en) | Introducer for intravascular graft | |
WO2005117754A1 (en) | Expandable and contractible guidewire | |
CA2609360A1 (en) | Mechanically actuated stents and apparatus and methods for delivering them | |
JP2010540194A (en) | Medical device with curved struts |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |