US20040093056A1 - Medical appliance delivery apparatus and method of use - Google Patents
Medical appliance delivery apparatus and method of use Download PDFInfo
- Publication number
- US20040093056A1 US20040093056A1 US10/281,429 US28142902A US2004093056A1 US 20040093056 A1 US20040093056 A1 US 20040093056A1 US 28142902 A US28142902 A US 28142902A US 2004093056 A1 US2004093056 A1 US 2004093056A1
- Authority
- US
- United States
- Prior art keywords
- tubular member
- stent
- deployment
- inner tubular
- outer tubular
- 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
- YHCZZOYAKKCRSQ-UHFFFAOYSA-N OCC1[IH][IH]CCCCCC[IH]CCC(CN=O)CC1 Chemical compound OCC1[IH][IH]CCCCCC[IH]CCC(CN=O)CC1 YHCZZOYAKKCRSQ-UHFFFAOYSA-N 0.000 description 1
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
-
- 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
- A61F2/9517—Instruments specially adapted for placement or removal of stents or stent-grafts handle assemblies therefor
-
- 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
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
- A61F2250/008—Alarm means
Definitions
- the present invention relates generally to medical devices directed to the prevention of nonvascular vessel or passageway occlusion, and more particularly to stent deployment apparatuses and methods for utilizing these devices in the treatment of both benign and malignant conditions.
- Stents are devices that are inserted into a vessel or passage to keep the lumen open and prevent closure due to a stricture, external compression, or internal obstruction.
- stents are commonly used to keep blood vessels open in the coronary arteries and they are frequently inserted into the ureters to maintain drainage from the kidneys, the bile duct for pancreatic cancer or cholangiocarcinoma or the esophagus for strictures or cancer.
- Nonvascular stenting involves a range of anatomical lumens and various therapeutic approaches, however, accuracy of installation is universally important.
- the stent In order to serve its desired function, the stent must be delivered precisely and oriented correctly. In order to facilitate the delivery of stents, medical device companies began to design deployment apparatuses that allow physicians to deploy stents more precisely. Unfortunately, guidance of the stent has substantially remained a function of physician skill resulting from substantial practice. This fact has become particularly evident with the advent of radially expanding stents. If after full deployment of the stent, the physician discovers the stent has been implanted incorrectly, there is no conventional way of correcting the error short of removing the stent. In particular, as a rule of thumb, once the exterior catheter, of conventional delivery devices, has been retracted beyond 60%, it generally cannot be realigned with respect to the stent. As a result, physicians must be sure of their stent placement prior to deploying the stent beyond the 60% point. We will refer to this 60% point throughout the application as the critical deployment point.
- An additional limitation of conventional stent delivery devices is the distal tip of conventional stent delivery devices are not adequately designed to (1) facilitate the clearance of obstructed lumen, or (2) facilitate the removal of the delivery device once the stent is radially expanded.
- most distal tips are not configured to comfortably guide the delivery device through a diseased or occluded lumen so that the stent can be delivered in the most beneficial location.
- conventional designs rely exclusively on dimensional mismatching to ensure proper removal of the delivery device. In the event the stent does not adequately expand to preset dimensions, a conventional delivery device would be stuck in the patient until some invasive procedure is performed to remove it and the defective stent.
- a stent deployment apparatuses that has a safety mechanism to prevent excessive deployment of a misaligned stent.
- the safety mechanism had a physical and/or audible indication means to inform the physician when she has reached maximum reversible deployment.
- a distal tip designed to allow for the removal of the deployment apparatus even if the stent does not radially expand to its preset expansion diameter.
- An existing need also exists for a stent deployment apparatus that has a distal tip adequately configured to navigate through diseased and/or occluded lumens so that the stent can be delivered to this target area.
- an exemplary stent deployment apparatus in accordance with the present invention to provide a device that can facilitate the precise delivery of stents in a safe and repeatable fashion.
- a preferred deployment apparatus allows the physician to concentrate on correct placement without having to estimate extent of deployment.
- the present deployment apparatus has a physical safety mechanism that limits deployment to the critical deployment point (i.e., ⁇ 60%).
- the critical deployment point may range form 5% to 95% but is preferably about 60%.
- the physician is satisfied with placement, she can engage the safety means to what we refer to as the Proceed Orientation (PO) and fully deploy the stent.
- PO Proceed Orientation
- the safety mechanism when the safety mechanism is engaged to the PO, a physical twist and a possible audible indicator sounds to inform the physician that if she deploys the stent any further, she can no longer retract the stent beyond this point.
- the present stent and delivery system eliminates the need for repositioning, such safety features are still preferable.
- the slight audible indication is the sound of a tab or stop snapping to allow free deployment of the stent.
- An additional objective of a preferred embodiment of the present invention is to provide a stent deployment apparatus where the handle portion is held and the outer tubular member of the device is retracted.
- Yet another objective in accordance with the present invention is to provide a deployment apparatus having a distal tip designed to facilitate the clearance of obstructed lumen.
- the exemplary distal tips are configured to comfortably guide the deployment apparatus through a diseased or occluded lumen so that the stent can be delivered in the most beneficial location.
- Still another objective of a preferred deployment apparatus in accordance with the present invention is to provide a distal tip that facilitates the removal of the deployment apparatus once the stent is radially expanded.
- the distal tip is designed to clear the stent during removal, in the event the stent does not adequately expand to preset dimensions.
- removal is facilitated by providing a distal tip that has a substantially bidirectional conic shape. This allows for the removal of the present deployment apparatus, while conventional deployment apparatuses would be stuck in the patient until some invasive procedure was performed to remove it and the defective stent.
- An additional objective in accordance with an exemplary embodiment of the present invention is to provide a stent deployment apparatus that allows for the insertion of an optical scope to facilitate stent delivery.
- the device is capable of letting a flexible optical scope of about 5-6 mm diameter be coupled along the exterior of the outer tubular member thereof.
- an ultra thin optical scope may pass along side the guidewire through the internal diameter of the internal tubular member of the device.
- an exemplary stent deployment apparatus preferably has one or more of the following characteristics: (1) applicable for various interventional applications such as addressing stenosis; (2) biocompatible; (3) compliant with radially expanding stents; (4) capable of distal or proximal stent release; (5) smooth and clean outer surface; (6) length of the device variable according to the insertion procedure to be employed; (7) outer dimension as small as possible (depends on the diameter of crimped stent); (8) dimensions of the device must offer enough space for the crimped stent; (9) radiopaque markers, preferably on the inner tubular member, to indicate proximal and distal ends of the stent; (10) sufficient flexibility to adopt to luminal curvatures without loss of ability to push or pull; (11) low friction between the inner tubular member and outer tubular member; (12) sufficient resistance to kinking; (13) good deployment, ability to reposition partially deployed stent; (14) added with a scale to observe the stent position
- FIG. 1 is a perspective view of a device for delivering and deploying a radially self-expanding stent in accordance with the present invention
- FIG. 2 is a side view of the device for delivering and deploying a radially self-expanding stent in accordance with the present invention.
- FIG. 3A depicts enlarged views of portions of the deployment safety mechanism along lines 3 A- 3 A of the device of FIG. 2
- FIG. 3B shows a cross section view of the deployment safety mechanism along lines 3 B- 3 B of FIG. 3A;
- FIG. 3C is a perspective view of a portion of the complementary portion of the deployment safety mechanism region of the handle as shown along lines 3 C- 3 C of FIG. 3A;
- FIG. 3D is a perspective view of the stop of the deployment safety mechanism as shown along lines 3 C- 3 C of the device of FIG. 3A.
- FIG. 4A is a side perspective view of the distal region of the device of FIG. 2, along lines 4 A- 4 A;
- FIG. 4B depict an enlarged sectional view of the distal region of the device of FIG. 2, along lines 4 B- 4 B.
- a general problem in the diagnosis and therapy of both vascular and nonvascular anomalies is the fact that the instruments must be inserted into or pass the area of maximum diameter of about 15 mm. As a result, the inserted instruments take away a very large portion of the free lumen and may increase the danger of injury to the patient.
- a preferred embodiment of the present deployment apparatus comprises inner and outer tubular members interactively coupled with each other in a manner that one can move rotationally and proximally or distally with respect to the other.
- the tubular members are preferably nonpyrogenic.
- the deployment apparatus comprises a distal tip and a stent retaining hub, between which the stent is placed.
- the distal tip and the stent-retaining hub are both functionally coupled with the inner tubular member.
- the inner tubular member terminates with a luer or in a preferred embodiment, a proximal handle similar to the outer handle hub.
- the luer is preferably a female threaded luer, but alternative termini are within the skill of the stent deployment device engineer.
- a suitable alternative would be a handle having similar internal diameter characteristics as the luer while providing greater surface area for manipulating the deployment apparatus.
- a preferred alternative would be a proximal handle that is similar in geometrical shape but preferably smaller than the outer handle hub, to facilitate movement, however the proximal handle may be of any size functionally acceptable by the user.
- the deployment apparatus is preferably sterilized by a validated sterilization cycle EtO.
- the device is capable of resterilization (validated cycle) with no degradation of performance.
- the deployment apparatus is preferably about 100 cm ⁇ 2 cm total.
- the inner diameter of the inner tubular member is approximately about 1 mm and the outer diameter of the outer tubular member is preferably about 5 to 6 mm in diameter.
- the usable length of the inner tubular member shall be from the inner tubular member distal hub/handle end to the distal tip.
- the usable length of the outer tubular member shall be from the distal hub/handle end of the outer tubular member to the distal tip.
- the overall length of the device shall be from the distal hub/handle end of the outer tubular member to the distal tip of the inner tubular member when assembled and not deployed.
- the outer tubular member is preferably manufactured of stiffer synthetic material. In a preferred embodiment, the length of the outer tubular member is preferably shorter than that of the inner tubular member.
- the outer tubular member may be configured to allow for the coupling of an optical stent along the outer diameter thereof.
- the inner diameter of the inner tubular member may be enlarged sufficiently to accommodate the optical scope and additionally the increased crimped stent diameter.
- the smallest diameter that allows for example a bronchoscope to pass will be employed in this alternative embodiment. It should be understood that through hindsight, after exposure to the present specification, one of ordinary skill would be able to adapt the current device to receive an ultra thin optical scope to the internal diameter of the device without undo experimentation and without departing from the spirit of the present objectives.
- An exemplary deployment apparatus in accordance with the present invention is durable while affording adequate flexibility to navigate through anatomical lumens without kinking.
- the deployment apparatus is formed of biocompatible synthetics and in a preferred embodiment reinforced with metal structure. This should allow for deployment within an accuracy of about ⁇ 3 mm.
- the stent is preferably released with a force lower than 30 Newtons at 37° C. though the force and deployment temperatures may be modified to suit the needs of specific anatomical conditions.
- the inner tubular member is composed of a thin elastic synthetic material, such as polyurethane or Teflon®. At its proximal end, the inner tubular member has a standard adaptor or connector. At its distal end, the inner tubular member is equipped with a tip specific for various anatomical lumens.
- the inner tubular member and the outer tubular member can be displaced relative to each other in longitudinal direction as well as in a radial direction.
- the deployment apparatus in accordance with the present invention can be used most advantageously for the placement of stents.
- stents are available in various embodiments of metal and/or synthetic material. They usually are composed of a fabric of metal wires, which expand by themselves as a result of their natural tension. Stents of a so-called shape memory alloy are also known. These stents have a small radial diameter at a low temperature, while they expand radially when exceeding an upper threshold temperature, so that they can keep a stenosis open in this manner. It is particularly advantageous to use stents of an alloy of nickel and titanium, the so-called nitinol.
- the outer tubular member when the stent is inserted and after the stenosis has been passed, the outer tubular member is retracted, so that the stent is released.
- the distal end of the outer tubular member may be placed about the stenosis so that the inner tubular member may be extended so that the stent is placed in direct contact with the desired location prior to expansion.
- a self-expanding stent then by itself assumes the expanded position. This eliminates the need for post expansion positioning techniques.
- the device has fasteners that retain contact with a portion of the stent in the event that the stent needs to be retracted or repositioned.
- a stent suitable for such procedures would be one in accordance with the disclosure in copending U.S. patent application Ser. No. 10/190,770, which is incorporated herein in its entirety by this reference.
- the figures show an exemplary placement and deployment device 10 in accordance with the present invention.
- the present invention provides a stent deployment apparatus 10 that includes an outer tubular member 50 and an inner tubular member 30 , wherein the outer tubular member 50 and the inner tubular member 30 can be displaced relative to each other.
- a threaded female luer 14 At the proximal end of an exemplary device 10 is a threaded female luer 14 , coupled with a portion of the inner tubular member 30 and preferably a portion of a hypotube 16 .
- a suitable alternative terminus may be employed as long as it provides the minimum benefits provided by a luer.
- the hypotube 16 is disposed about the inner tube 30 and extends from a location adjacent to the luer 14 through a portion of the handle 40 of the deployment apparatus 10 .
- the hypotube 16 terminates within the luer 14 .
- a safety mechanism 18 is provided that is formed in part by the complementary fitting of a portion of the handle 40 and a stop 20 coupled with the hypotube 16 between the luer 14 and the handle 40 .
- the stop 20 is preferably molded onto the hypotube 16 , the molding process resulting in a tab 24 formed on the stop 20 that is subsequently broken when the physician desires to place the deployment apparatus 10 in the proceed orientation.
- the stop 20 when the tab 24 is broken and the deployment apparatus 10 is placed in the proceed orientation; the stop 20 may potentially rotate freely about the hypotube 16 . It should be kept in mind that the stop 20 may take a variety of shapes, including but not limited to, rectangular, round, conical etc. In a preferred embodiment, the stop 20 is conical with a tapered effect to facilitate entrance and removal from the base handle cavity 44 .
- a preferred stop 20 includes female locking members 22 comprising channels formed along the exterior thereof that are complementary to the male locking members 46 formed on the interior cavity 42 along the proximal region of the handle 40 .
- the cavity 42 of the handle 40 is designed to receive the stop 20 and prevent further deployment.
- the stop 20 is molded at a distance along the hypotube 16 such that the distance between the distal end of the stop and the base 44 of the complementary cavity 42 of the handle 40 roughly corresponds to the critical deployment point.
- the female locking members 22 and male locking members 46 of the safety mechanism 18 might be reversed so that the female locking members 22 and male locking members 46 are on the handle 40 and the stop 20 , respectively.
- alternative safety mechanisms may be employed to ensure accurate deployment beyond the critical deployment point.
- the handle 40 is preferably molded to a portion of the outer tubular member 50 , which extends from the handle 40 to the distal tip 60 of the device 10 .
- the outer tubular member 50 is disposed about the inner tubular member 30 .
- the outer tubular member 50 is clear so that the inner tubular member 50 is visible there through.
- markers 80 - 84 preferably formed on portions of the inner tubular member 30 are also visible through the outer tubular member 50 .
- the stent placement hub 70 which holds the stent (not shown) during the placement procedure.
- the stent placement hub 70 comprises two double conical shaped elements, one disposed at each end of the stent and coupled with the inner tubular member 30 .
- the distal most double conical shaped element is the distal tip of the device 60 .
- the stent placement hub may also comprise proximal 72 and distal 74 stops between which the stent rests in its crimped state.
- proximal end of the stent may also be restrained by conventional coupling methods (not shown) to facilitate retrieval if necessary.
- a stent having suture disposed about its proximal end may be retained by the stent retaining hub 70 that has releasable finger-like members engaging the suture.
- the device is configured such that an optional guidewire 12 may be passed through the internal diameter 32 of the device through the luer 14 at the proximal end, the distal tip 60 at the distal end and the inner tubular member 30 there between.
- the internal diameter 32 of the device 10 is sufficient to receive an optical scope (not shown) there through.
- FIG. 1 a deployment apparatus 10 that includes an elongate and flexible outer tubular member 50 constructed of at least one biocompatible thermoplastic elastomer, e.g. such as polyurethane and nylon, typically with an outside diameter 52 in the range of about between 6-9 mm.
- a central lumen 56 runs the length of the outer tubular member 50 .
- a distal region 54 of the outer tubular member 50 surrounds the stent to be placed (not shown), and maintains the stent in a crimped delivery configuration, against an elastic restoring force of the stent.
- the stent when in a normal unrestrained configuration, generally has a diameter (for example, 10-20 mm) substantially larger than the interior diameter 32 of the inner tubular member 30 .
- the expanded stent is larger in diameter than the body lumen in which the stent is fixed, and the restoring force tends to maintain the stent against the tissue wall.
- Outer tubular member 50 is mounted at its proximal end to a handle 40 .
- Outer tubular member 50 can be pushed and pulled relative to inner tubular member 30 by hand manipulation of the handle 40 at the proximal end of the outer tubular member 30 and holding the proximal end of the handle 40 .
- a guidewire 12 is preferably disposed within the interior lumen 32 of an elongate and flexible inner tubular member 30 , which can be constructed of materials similar to those employed to form the outer tubular member 50 . However, it is preferable that inner tubular member 30 is formed from a more durable material.
- a distal tip 60 is coupled with inner tubular member 30 about the distal end thereof.
- Also attached to the inner tubular member 30 are a proximal marker 80 , at least one medial marker 82 and a distal marker 84 .
- the markers are constructed of a radiopaque material, e.g. platinum iridium, and surround the inner tubular member 30 .
- Markers 80 , 82 and 84 are axially spaced apart to mark the length of the stent and to mark the critical deployment distance for that stent length.
- the markers identify a stent-retaining hub 0 . 70 of the inner tubular member 30 , more particularly the distal region of the inner tubular member 30 is surrounded by stent 12 .
- the markers may also be of varying sizes and shapes to distinguish distance between distal and proximal regions.
- Markers 80 and 84 may have outer diameters slightly smaller than the interior diameter of outer tubular member 50 .
- the outer tubular member 50 thus functions as a carrier for the stent, with inner tubular member 30 providing a retaining means for radially compressing the stent and maintaining the stent along the stent retaining hub 50 , so long as the outer tubular member 50 surrounds the stent.
- items 72 and 74 are marker bands (not retaining hubs) formed on the outer tubular member 50 . These marker bands visually mark the ends of the stent and thus will be over the step area of the tip and the pusher 76 . All the marker bands including 80 , 82 and 84 are preferably either Platinum Iridium or Stainless Steel. Moreover, the marker bands of 80 , 82 , and 84 will be depth marks and will be spaced in preferably 1 cm intervals. These depth marks are preferably formed on the inner tubular member 30 and are a visual aid for the physician to assist with determining the depth at which the stent has been advanced.
- Inner tubular member 30 along its entire length, has an interior lumen 56 open to both the proximal and distal ends of the inner tubular member 30 .
- An axial passage 68 through distal tip 60 continues lumen 32 to allow the guidewire 12 to pass from the luer 14 through the distal tip 60 .
- Handle 40 and outer tubular member 50 are movable relative to inner tubular member 30 . More particularly, the handle 40 is moved proximally relative to the stent-retaining hub 70 , facilitating the movement of outer tubular member 50 relative to inner tubular member 30 so as to provide a means for controllably withdrawing the outer tubular member 50 , relative to the inner tubular member 30 , resulting in the release of the stent for radial self-expansion.
- the initial step is to position guidewire 12 within the anatomy of a patient. This can be accomplished with a guide cannula (not illustrated), leaving guidewire 12 in place, with the exchange portion of the guidewire extended proximally beyond the point of entry into the anatomy of the patient. Deployment apparatus 10 is then advanced over the guidewire 12 at the exchange portion, with the guidewire 12 being received into passage 68 of distal tip 60 . As device 10 is inserted into the body, the proximal portion of guidewire 12 travels proximally (relative to the device) to the proximal end of guidewire lumen 32 .
- the physician maintains guidewire 12 and inner tubular member 30 substantially fixed with one hand, while moving handle 40 in the proximal direction with the other hand, thus to move outer tubular member 50 proximally relative to inner tubular member 30 .
- the stent remains substantially fixed relative to inner tubular member 30 , and thus radially self-expands.
- the handle 40 and correspondingly the outer tubular member 50 is retracted, the handle 40 encounters the safety mechanism 18 for the critical deployment point.
- the inner tubular member 30 via the handle 40 , may have to be rotated to align and insert the stop 20 into the handle 40 . When fully inserted, further deployment cannot occur without twisting and snapping the stop the tab 24 portion of the stop 20 . Continued retraction of the outer tubular member 50 results in complete deployment of the stent.
- the stent After deployment, the stent ideally radially self-expands to a diameter greater than the diameter of outer tubular member 50 . Accordingly, device 10 can be withdrawn proximally through the stent. However, in the event that the stent does not radially expand fully, distal tip 60 is configured to facilitate removal of deployment apparatus 10 through the lumen of the stent.
- Guidewire 12 can be withdrawn as well.
- the guidewire 12 emerges from the proximal end of the luer 14 .
- the deployment apparatus 10 can be removed without removing the guidewire 12 .
- Device 10 is removed by progressively pulling the device away from the guidewire 12 (which removes the guidewire from within the inner tubular member 30 ), all while maintaining guidewire 12 in place.
- distal tip 60 can have a variety of confirmations, but by way of non-limiting example, distal tip 60 comprises first 62 and second 66 ends having a smaller diameter than the medial region 64 thereof.
- each end is conical in shape so as to allow the tip 60 to wedge through an incompletely expanded stent when pulled proximally with respect to the stent.
- the dual conical end design facilitates removal but sufficiently prevents the crimped stent from releasing from the stent retaining hub 70 and prematurely expanding.
- Distal tip 60 may alternatively have a flared medial region 64 so as to facilitate retrieval and retraction of a misaligned stent 12 .
- the device 10 has a deployment safety mechanism 18 that comprises male 46 and female 22 locking members that are brought into functional engagement as the stent is being deployed. Once the stent has reached the critical deployment point, the distal end of the stop 20 is substantially flush with the base 44 of the handle cavity 42 and the female locking members 22 of the stop 20 are in operative communication with the corresponding male locking members 46 formed on the interior surface of the cavity 42 of the handle.
- the safety mechanism 18 is engaged as described above, the stent cannot be deployed further without physician intervention. In order to deploy the stent beyond this point, the physician has to rotate the stop 20 to cause the tab 24 to break. Once the tab 24 is broken, the device 10 is in the proceed orientation and deployment may proceed.
- the physician will feel a tactile indication that the device 10 can be deployed further.
- the breaking of the tab may also, or as a substitute to tactile indication, results in an audible indication that further deployment is possible.
- the physician is apprised of the fact that deployment beyond this point is irreversible except for interventional retrieval methods.
- the critical deployment point is preferably about 60% deployment, beyond which retraction is not recommended.
- the safety mechanism 18 removes the need to estimate extent of deployment and provides a reliable means of accurately deploying stents.
- Alternative locking mechanisms may be provided as long as they retain the important characteristic of giving the physician a sensory indication of extent of stent deployment and removes the need to estimate extent of deployment.
- the locking mechanism could comprise a breakable seal, tab/stop lock, diverted channel locking mechanism, etc.
- an alternative safety mechanism 118 is presented that is a principally a diverted channel mechanism.
- a detent 90 formed preferably on the hypotube has free proximal/distal travel to the critical deployment point at which time physician intervention is required to continue deployment.
- the Inner Tubular Member 30 is rotated until the travel of the detent is no longer obstructed.
- the channel in which the detent travels may be of a variety of geometrical shapes such as M, W, L, S Z, etc; the preferred geometry being substantially Z shaped, as shown in FIG. 5.
- the device 10 has a deployment safety mechanism that comprises male and female locking members that are brought into functional engagement as the stent 12 is being deployed. Once the stent 12 has reached the critical deployment point, the male locking member cannot be advanced further because of a detent formed on the inner diameter of the outer tubular member catches the cavity formed on the corresponding portion of the male locking member. As a result, in order to further advance the device 10 to fully deploy stent 12 , the inner tubular member must be rotated so as to break the detent. Once the detent is broken, the physician will feel a tactile indication that the device 10 can be deployed further.
- the breaking of the detent may also, or as a substitute to tactile indication, results in an audible indication that further deployment is possible.
- the physician is apprised of the fact that deployment beyond this point is irreversible except for interventional retrieval methods.
- the critical deployment point is preferably about 60% deployment, beyond which retraction is not recommended.
- the safety locking system 60 removes the need to estimate extent of deployment and provides a reliable means of accurately deploying stents.
- Alternative locking mechanisms may be provided as long as they retain the important characteristic of giving the physician a sensory indication of extent of stent deployment.
Abstract
Description
- The present invention relates generally to medical devices directed to the prevention of nonvascular vessel or passageway occlusion, and more particularly to stent deployment apparatuses and methods for utilizing these devices in the treatment of both benign and malignant conditions.
- Stents are devices that are inserted into a vessel or passage to keep the lumen open and prevent closure due to a stricture, external compression, or internal obstruction. In particular, stents are commonly used to keep blood vessels open in the coronary arteries and they are frequently inserted into the ureters to maintain drainage from the kidneys, the bile duct for pancreatic cancer or cholangiocarcinoma or the esophagus for strictures or cancer. Nonvascular stenting involves a range of anatomical lumens and various therapeutic approaches, however, accuracy of installation is universally important.
- In order to serve its desired function, the stent must be delivered precisely and oriented correctly. In order to facilitate the delivery of stents, medical device companies began to design deployment apparatuses that allow physicians to deploy stents more precisely. Unfortunately, guidance of the stent has substantially remained a function of physician skill resulting from substantial practice. This fact has become particularly evident with the advent of radially expanding stents. If after full deployment of the stent, the physician discovers the stent has been implanted incorrectly, there is no conventional way of correcting the error short of removing the stent. In particular, as a rule of thumb, once the exterior catheter, of conventional delivery devices, has been retracted beyond 60%, it generally cannot be realigned with respect to the stent. As a result, physicians must be sure of their stent placement prior to deploying the stent beyond the 60% point. We will refer to this 60% point throughout the application as the critical deployment point.
- Conventional stent delivery devices, however, do not have any safety mechanism to prevent excessive deployment of a misaligned stent. In fact, conventional delivery devices require the physician to estimate extent of deployment, which results in either overly conservative or excessive deployment—both of which leads to stent misplacement.
- An additional limitation of conventional stent delivery devices is the distal tip of conventional stent delivery devices are not adequately designed to (1) facilitate the clearance of obstructed lumen, or (2) facilitate the removal of the delivery device once the stent is radially expanded. In particular, most distal tips are not configured to comfortably guide the delivery device through a diseased or occluded lumen so that the stent can be delivered in the most beneficial location. Moreover, once the stent is radially expanded conventional designs rely exclusively on dimensional mismatching to ensure proper removal of the delivery device. In the event the stent does not adequately expand to preset dimensions, a conventional delivery device would be stuck in the patient until some invasive procedure is performed to remove it and the defective stent.
- Therefore, there remains an existing need for a stent deployment apparatuses that has a safety mechanism to prevent excessive deployment of a misaligned stent. Preferably it would be desirable if the safety mechanism had a physical and/or audible indication means to inform the physician when she has reached maximum reversible deployment. As an additional safety feature, there is an existing need for a distal tip designed to allow for the removal of the deployment apparatus even if the stent does not radially expand to its preset expansion diameter. An existing need also exists for a stent deployment apparatus that has a distal tip adequately configured to navigate through diseased and/or occluded lumens so that the stent can be delivered to this target area.
- There also remains an existing need for a stent deployment apparatus that increases physician control during stent deployment. Moreover, there exists a need for a stent deployment apparatus that allows for the insertion of an optical scope to facilitate stent delivery.
- It is a principal objective of an exemplary stent deployment apparatus in accordance with the present invention to provide a device that can facilitate the precise delivery of stents in a safe and repeatable fashion. In the furtherance of this and other objectives, a preferred deployment apparatus allows the physician to concentrate on correct placement without having to estimate extent of deployment. In particular, in a preferred embodiment, the present deployment apparatus has a physical safety mechanism that limits deployment to the critical deployment point (i.e., −60%). The critical deployment point may range form 5% to 95% but is preferably about 60%. At this point, if the physician is satisfied with placement, she can engage the safety means to what we refer to as the Proceed Orientation (PO) and fully deploy the stent. It is preferred that when the safety mechanism is engaged to the PO, a physical twist and a possible audible indicator sounds to inform the physician that if she deploys the stent any further, she can no longer retract the stent beyond this point. Though the present stent and delivery system eliminates the need for repositioning, such safety features are still preferable. In a preferred embodiment, the slight audible indication is the sound of a tab or stop snapping to allow free deployment of the stent.
- An additional objective of a preferred embodiment of the present invention is to provide a stent deployment apparatus where the handle portion is held and the outer tubular member of the device is retracted.
- Yet another objective in accordance with the present invention is to provide a deployment apparatus having a distal tip designed to facilitate the clearance of obstructed lumen. In the furtherance of this and other objectives, the exemplary distal tips are configured to comfortably guide the deployment apparatus through a diseased or occluded lumen so that the stent can be delivered in the most beneficial location.
- Still another objective of a preferred deployment apparatus in accordance with the present invention is to provide a distal tip that facilitates the removal of the deployment apparatus once the stent is radially expanded. In the furtherance of this and other objectives, the distal tip is designed to clear the stent during removal, in the event the stent does not adequately expand to preset dimensions. In a preferred embodiment, removal is facilitated by providing a distal tip that has a substantially bidirectional conic shape. This allows for the removal of the present deployment apparatus, while conventional deployment apparatuses would be stuck in the patient until some invasive procedure was performed to remove it and the defective stent. This results from the fact that conventional deployment apparatus designs rely exclusively on dimensional mismatching between the distal tip and the radially expanded stent to ensure proper removal of the deployment apparatus. As a function of the design of the present invention, the compressed stent is adequately retained in place and does not prematurely creep up the proximally facing conic end of the distal tip and prematurely deploy.
- An additional objective in accordance with an exemplary embodiment of the present invention is to provide a stent deployment apparatus that allows for the insertion of an optical scope to facilitate stent delivery. In the furtherance of this and other objectives, the device is capable of letting a flexible optical scope of about 5-6 mm diameter be coupled along the exterior of the outer tubular member thereof. Alternatively, it is envisioned that an ultra thin optical scope may pass along side the guidewire through the internal diameter of the internal tubular member of the device.
- In addition to the above objectives, an exemplary stent deployment apparatus preferably has one or more of the following characteristics: (1) applicable for various interventional applications such as addressing stenosis; (2) biocompatible; (3) compliant with radially expanding stents; (4) capable of distal or proximal stent release; (5) smooth and clean outer surface; (6) length of the device variable according to the insertion procedure to be employed; (7) outer dimension as small as possible (depends on the diameter of crimped stent); (8) dimensions of the device must offer enough space for the crimped stent; (9) radiopaque markers, preferably on the inner tubular member, to indicate proximal and distal ends of the stent; (10) sufficient flexibility to adopt to luminal curvatures without loss of ability to push or pull; (11) low friction between the inner tubular member and outer tubular member; (12) sufficient resistance to kinking; (13) good deployment, ability to reposition partially deployed stent; (14) added with a scale to observe the stent position during the insertion procedure; (15) insertion procedure should require low force; or (16) sufficiently economical to manufacture so as to make the deployment apparatus disposable.
- Further objectives, features and advantages of the invention will be apparent from the following detailed description taken in conjunction with the accompanying drawings.
- FIG. 1 is a perspective view of a device for delivering and deploying a radially self-expanding stent in accordance with the present invention;
- FIG. 2 is a side view of the device for delivering and deploying a radially self-expanding stent in accordance with the present invention.
- FIG. 3A depicts enlarged views of portions of the deployment safety mechanism along
lines 3A-3A of the device of FIG. 2 - FIG. 3B shows a cross section view of the deployment safety mechanism along
lines 3B-3B of FIG. 3A; - FIG. 3C is a perspective view of a portion of the complementary portion of the deployment safety mechanism region of the handle as shown along
lines 3C-3C of FIG. 3A; - FIG. 3D is a perspective view of the stop of the deployment safety mechanism as shown along
lines 3C-3C of the device of FIG. 3A. - FIG. 4A is a side perspective view of the distal region of the device of FIG. 2, along
lines 4A-4A; - FIG. 4B depict an enlarged sectional view of the distal region of the device of FIG. 2, along
lines 4B-4B. - A general problem in the diagnosis and therapy of both vascular and nonvascular anomalies is the fact that the instruments must be inserted into or pass the area of maximum diameter of about 15 mm. As a result, the inserted instruments take away a very large portion of the free lumen and may increase the danger of injury to the patient.
- Therefore, it is the primary objective of the present invention to provide an instrument, which can be inserted gently, ensures a good utilization of the available space and makes it possible to carry out active therapeutic measures, wherein the instrument is to be particularly suitable for the introduction and placement of stents.
- A preferred embodiment of the present deployment apparatus comprises inner and outer tubular members interactively coupled with each other in a manner that one can move rotationally and proximally or distally with respect to the other. The tubular members are preferably nonpyrogenic. In order to deliver the stent, the deployment apparatus comprises a distal tip and a stent retaining hub, between which the stent is placed. The distal tip and the stent-retaining hub are both functionally coupled with the inner tubular member. The inner tubular member terminates with a luer or in a preferred embodiment, a proximal handle similar to the outer handle hub. The luer is preferably a female threaded luer, but alternative termini are within the skill of the stent deployment device engineer. In fact, a suitable alternative would be a handle having similar internal diameter characteristics as the luer while providing greater surface area for manipulating the deployment apparatus. As stated above, a preferred alternative would be a proximal handle that is similar in geometrical shape but preferably smaller than the outer handle hub, to facilitate movement, however the proximal handle may be of any size functionally acceptable by the user. The deployment apparatus is preferably sterilized by a validated sterilization cycle EtO. Moreover, the device is capable of resterilization (validated cycle) with no degradation of performance. However, it is preferable to provide a disposable device.
- The deployment apparatus is preferably about 100 cm±2 cm total. The inner diameter of the inner tubular member is approximately about 1 mm and the outer diameter of the outer tubular member is preferably about 5 to 6 mm in diameter. For purposes of this discussion, the usable length of the inner tubular member shall be from the inner tubular member distal hub/handle end to the distal tip. The usable length of the outer tubular member shall be from the distal hub/handle end of the outer tubular member to the distal tip. The overall length of the device shall be from the distal hub/handle end of the outer tubular member to the distal tip of the inner tubular member when assembled and not deployed. There will also be preferably three radiopaque (platinum iridium) markers for marking the stent, the stent deployment distance, and depth. The outer tubular member is preferably manufactured of stiffer synthetic material. In a preferred embodiment, the length of the outer tubular member is preferably shorter than that of the inner tubular member.
- However, these dimensions may differ as a function of the stent diameter and/or if an optical scope is employed to facilitate stent delivery. The outer tubular member may be configured to allow for the coupling of an optical stent along the outer diameter thereof. Alternatively, the inner diameter of the inner tubular member may be enlarged sufficiently to accommodate the optical scope and additionally the increased crimped stent diameter. However, it is expected, though not required, that the smallest diameter that allows for example a bronchoscope to pass will be employed in this alternative embodiment. It should be understood that through hindsight, after exposure to the present specification, one of ordinary skill would be able to adapt the current device to receive an ultra thin optical scope to the internal diameter of the device without undo experimentation and without departing from the spirit of the present objectives.
- An exemplary deployment apparatus in accordance with the present invention is durable while affording adequate flexibility to navigate through anatomical lumens without kinking. To this end, it is preferable that the deployment apparatus is formed of biocompatible synthetics and in a preferred embodiment reinforced with metal structure. This should allow for deployment within an accuracy of about ±3 mm. Moreover, the stent is preferably released with a force lower than 30 Newtons at 37° C. though the force and deployment temperatures may be modified to suit the needs of specific anatomical conditions.
- The inner tubular member is composed of a thin elastic synthetic material, such as polyurethane or Teflon®. At its proximal end, the inner tubular member has a standard adaptor or connector. At its distal end, the inner tubular member is equipped with a tip specific for various anatomical lumens.
- The inner tubular member and the outer tubular member can be displaced relative to each other in longitudinal direction as well as in a radial direction. The deployment apparatus in accordance with the present invention can be used most advantageously for the placement of stents. Such stents are available in various embodiments of metal and/or synthetic material. They usually are composed of a fabric of metal wires, which expand by themselves as a result of their natural tension. Stents of a so-called shape memory alloy are also known. These stents have a small radial diameter at a low temperature, while they expand radially when exceeding an upper threshold temperature, so that they can keep a stenosis open in this manner. It is particularly advantageous to use stents of an alloy of nickel and titanium, the so-called nitinol.
- An exemplary deployment apparatus according to the present invention can be used for the placement of various stents, whether they are self-expanding stents or stents, which require an activation. For this purpose, the stent is placed in the free space between the outer tubular member and the inner tubular member. Positioning of the stent in the deployment apparatus can be carried out in the area between the tip and the stent retaining hub at the distal end of the inner tubular member. Alternatively, in its insertion position, fasteners or other suitable retaining elements may hold the stent.
- In relevant embodiments, when the stent is inserted and after the stenosis has been passed, the outer tubular member is retracted, so that the stent is released. Alternatively, the distal end of the outer tubular member may be placed about the stenosis so that the inner tubular member may be extended so that the stent is placed in direct contact with the desired location prior to expansion. A self-expanding stent then by itself assumes the expanded position. This eliminates the need for post expansion positioning techniques. With an alternative embodiment of the device, the device has fasteners that retain contact with a portion of the stent in the event that the stent needs to be retracted or repositioned. A stent suitable for such procedures would be one in accordance with the disclosure in copending U.S. patent application Ser. No. 10/190,770, which is incorporated herein in its entirety by this reference.
- The following reference numbers and corresponding stent placement and deployment device components are used when describing the device in relation to the figures:
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
-
- The figures show an exemplary placement and
deployment device 10 in accordance with the present invention. Referring in particular to FIGS. 1-2, the present invention provides astent deployment apparatus 10 that includes anouter tubular member 50 and aninner tubular member 30, wherein the outertubular member 50 and theinner tubular member 30 can be displaced relative to each other. At the proximal end of anexemplary device 10 is a threadedfemale luer 14, coupled with a portion of theinner tubular member 30 and preferably a portion of ahypotube 16. As stated earlier, a suitable alternative terminus may be employed as long as it provides the minimum benefits provided by a luer. Thehypotube 16 is disposed about theinner tube 30 and extends from a location adjacent to theluer 14 through a portion of thehandle 40 of thedeployment apparatus 10. In an alternative embodiment, thehypotube 16 terminates within theluer 14. A safety mechanism 18 is provided that is formed in part by the complementary fitting of a portion of thehandle 40 and astop 20 coupled with thehypotube 16 between theluer 14 and thehandle 40. Thestop 20 is preferably molded onto thehypotube 16, the molding process resulting in atab 24 formed on thestop 20 that is subsequently broken when the physician desires to place thedeployment apparatus 10 in the proceed orientation. In an exemplary embodiment, when thetab 24 is broken and thedeployment apparatus 10 is placed in the proceed orientation; thestop 20 may potentially rotate freely about thehypotube 16. It should be kept in mind that thestop 20 may take a variety of shapes, including but not limited to, rectangular, round, conical etc. In a preferred embodiment, thestop 20 is conical with a tapered effect to facilitate entrance and removal from thebase handle cavity 44. - As illustrated in FIGS.3A-3D, a
preferred stop 20 includesfemale locking members 22 comprising channels formed along the exterior thereof that are complementary to themale locking members 46 formed on theinterior cavity 42 along the proximal region of thehandle 40. Thecavity 42 of thehandle 40 is designed to receive thestop 20 and prevent further deployment. As a result, thestop 20 is molded at a distance along thehypotube 16 such that the distance between the distal end of the stop and thebase 44 of thecomplementary cavity 42 of thehandle 40 roughly corresponds to the critical deployment point. It should be noted that thefemale locking members 22 andmale locking members 46 of the safety mechanism 18 might be reversed so that thefemale locking members 22 andmale locking members 46 are on thehandle 40 and thestop 20, respectively. Additionally, alternative safety mechanisms may be employed to ensure accurate deployment beyond the critical deployment point. - The
handle 40 is preferably molded to a portion of the outertubular member 50, which extends from thehandle 40 to thedistal tip 60 of thedevice 10. The outertubular member 50 is disposed about theinner tubular member 30. In an exemplary embodiment, the outertubular member 50 is clear so that theinner tubular member 50 is visible there through. Moreover, markers 80-84 preferably formed on portions of theinner tubular member 30 are also visible through the outertubular member 50. - Referring now to FIGS.4A-4B, in the
distal region 54 of thedevice 10, there is astent placement hub 70, which holds the stent (not shown) during the placement procedure. In a preferred embodiment, thestent placement hub 70 comprises two double conical shaped elements, one disposed at each end of the stent and coupled with theinner tubular member 30. In an exemplary form, the distal most double conical shaped element is the distal tip of thedevice 60. In alternative embodiments, the stent placement hub may also comprise proximal 72 and distal 74 stops between which the stent rests in its crimped state. Moreover, the proximal end of the stent may also be restrained by conventional coupling methods (not shown) to facilitate retrieval if necessary. By way of example, which is in no way to be construed as limiting, a stent having suture disposed about its proximal end may be retained by thestent retaining hub 70 that has releasable finger-like members engaging the suture. - The device is configured such that an
optional guidewire 12 may be passed through theinternal diameter 32 of the device through theluer 14 at the proximal end, thedistal tip 60 at the distal end and theinner tubular member 30 there between. In an alternative embodiment, theinternal diameter 32 of thedevice 10 is sufficient to receive an optical scope (not shown) there through. - Referring to the functional aspects of the
device 10, there is shown in FIG. 1 adeployment apparatus 10 that includes an elongate and flexible outertubular member 50 constructed of at least one biocompatible thermoplastic elastomer, e.g. such as polyurethane and nylon, typically with anoutside diameter 52 in the range of about between 6-9 mm. Acentral lumen 56 runs the length of the outertubular member 50. Adistal region 54 of the outertubular member 50 surrounds the stent to be placed (not shown), and maintains the stent in a crimped delivery configuration, against an elastic restoring force of the stent. The stent, when in a normal unrestrained configuration, generally has a diameter (for example, 10-20 mm) substantially larger than theinterior diameter 32 of theinner tubular member 30. Typically the expanded stent is larger in diameter than the body lumen in which the stent is fixed, and the restoring force tends to maintain the stent against the tissue wall. -
Outer tubular member 50 is mounted at its proximal end to ahandle 40. Outertubular member 50 can be pushed and pulled relative to innertubular member 30 by hand manipulation of thehandle 40 at the proximal end of the outertubular member 30 and holding the proximal end of thehandle 40. - A
guidewire 12 is preferably disposed within theinterior lumen 32 of an elongate and flexible innertubular member 30, which can be constructed of materials similar to those employed to form the outertubular member 50. However, it is preferable that innertubular member 30 is formed from a more durable material. Adistal tip 60 is coupled with innertubular member 30 about the distal end thereof. Also attached to theinner tubular member 30 are aproximal marker 80, at least onemedial marker 82 and adistal marker 84. The markers are constructed of a radiopaque material, e.g. platinum iridium, and surround theinner tubular member 30.Markers inner tubular member 30, more particularly the distal region of theinner tubular member 30 is surrounded bystent 12. The markers may also be of varying sizes and shapes to distinguish distance between distal and proximal regions.Markers tubular member 50. The outertubular member 50 thus functions as a carrier for the stent, with innertubular member 30 providing a retaining means for radially compressing the stent and maintaining the stent along thestent retaining hub 50, so long as the outertubular member 50 surrounds the stent. - In an alternative embodiment,
items tubular member 50. These marker bands visually mark the ends of the stent and thus will be over the step area of the tip and thepusher 76. All the marker bands including 80, 82 and 84 are preferably either Platinum Iridium or Stainless Steel. Moreover, the marker bands of 80, 82, and 84 will be depth marks and will be spaced in preferably 1 cm intervals. These depth marks are preferably formed on theinner tubular member 30 and are a visual aid for the physician to assist with determining the depth at which the stent has been advanced. -
Inner tubular member 30, along its entire length, has aninterior lumen 56 open to both the proximal and distal ends of theinner tubular member 30. Anaxial passage 68 throughdistal tip 60 continueslumen 32 to allow theguidewire 12 to pass from theluer 14 through thedistal tip 60. -
Handle 40 and outertubular member 50 are movable relative to innertubular member 30. More particularly, thehandle 40 is moved proximally relative to the stent-retaininghub 70, facilitating the movement of outertubular member 50 relative to innertubular member 30 so as to provide a means for controllably withdrawing the outertubular member 50, relative to theinner tubular member 30, resulting in the release of the stent for radial self-expansion. - When the
device 10 is used to position the stent, the initial step is to positionguidewire 12 within the anatomy of a patient. This can be accomplished with a guide cannula (not illustrated), leavingguidewire 12 in place, with the exchange portion of the guidewire extended proximally beyond the point of entry into the anatomy of the patient.Deployment apparatus 10 is then advanced over theguidewire 12 at the exchange portion, with theguidewire 12 being received intopassage 68 ofdistal tip 60. Asdevice 10 is inserted into the body, the proximal portion ofguidewire 12 travels proximally (relative to the device) to the proximal end ofguidewire lumen 32. - Once
device 10 is positioned, the physician maintainsguidewire 12 and innertubular member 30 substantially fixed with one hand, while movinghandle 40 in the proximal direction with the other hand, thus to move outertubular member 50 proximally relative to innertubular member 30. As the outertubular member 50 is retracted, the stent remains substantially fixed relative to innertubular member 30, and thus radially self-expands. As thehandle 40 and correspondingly the outertubular member 50 is retracted, thehandle 40 encounters the safety mechanism 18 for the critical deployment point. Theinner tubular member 30, via thehandle 40, may have to be rotated to align and insert thestop 20 into thehandle 40. When fully inserted, further deployment cannot occur without twisting and snapping the stop thetab 24 portion of thestop 20. Continued retraction of the outertubular member 50 results in complete deployment of the stent. - After deployment, the stent ideally radially self-expands to a diameter greater than the diameter of outer
tubular member 50. Accordingly,device 10 can be withdrawn proximally through the stent. However, in the event that the stent does not radially expand fully,distal tip 60 is configured to facilitate removal ofdeployment apparatus 10 through the lumen of the stent. - Guidewire12 can be withdrawn as well. The
guidewire 12 emerges from the proximal end of theluer 14. However, should the medical procedure involve further treatment, e.g., placement of a further stent, thedeployment apparatus 10 can be removed without removing theguidewire 12.Device 10 is removed by progressively pulling the device away from the guidewire 12 (which removes the guidewire from within the inner tubular member 30), all while maintainingguidewire 12 in place. - Returning to
distal tip 60, as illustrated in FIGS. 4A-4B,distal tip 60 can have a variety of confirmations, but by way of non-limiting example,distal tip 60 comprises first 62 and second 66 ends having a smaller diameter than themedial region 64 thereof. In a preferred embodiment, each end is conical in shape so as to allow thetip 60 to wedge through an incompletely expanded stent when pulled proximally with respect to the stent. Moreover, the dual conical end design facilitates removal but sufficiently prevents the crimped stent from releasing from thestent retaining hub 70 and prematurely expanding.Distal tip 60 may alternatively have a flaredmedial region 64 so as to facilitate retrieval and retraction of amisaligned stent 12. - With respect to additional safety features incorporated in the
present device 10, in a preferred embodiment, thedevice 10 has a deployment safety mechanism 18 that comprises male 46 and female 22 locking members that are brought into functional engagement as the stent is being deployed. Once the stent has reached the critical deployment point, the distal end of thestop 20 is substantially flush with thebase 44 of thehandle cavity 42 and thefemale locking members 22 of thestop 20 are in operative communication with the correspondingmale locking members 46 formed on the interior surface of thecavity 42 of the handle. When the safety mechanism 18 is engaged as described above, the stent cannot be deployed further without physician intervention. In order to deploy the stent beyond this point, the physician has to rotate thestop 20 to cause thetab 24 to break. Once thetab 24 is broken, thedevice 10 is in the proceed orientation and deployment may proceed. - In a preferred embodiment, the physician will feel a tactile indication that the
device 10 can be deployed further. Alternatively, the breaking of the tab may also, or as a substitute to tactile indication, results in an audible indication that further deployment is possible. Additionally, the physician is apprised of the fact that deployment beyond this point is irreversible except for interventional retrieval methods. As discussed earlier, the critical deployment point is preferably about 60% deployment, beyond which retraction is not recommended. As a result, the safety mechanism 18 removes the need to estimate extent of deployment and provides a reliable means of accurately deploying stents. Alternative locking mechanisms may be provided as long as they retain the important characteristic of giving the physician a sensory indication of extent of stent deployment and removes the need to estimate extent of deployment. By way of non-limiting example only, the locking mechanism could comprise a breakable seal, tab/stop lock, diverted channel locking mechanism, etc. - Referring particularly to FIG. 5, an
alternative safety mechanism 118 is presented that is a principally a diverted channel mechanism. In practice, adetent 90 formed preferably on the hypotube has free proximal/distal travel to the critical deployment point at which time physician intervention is required to continue deployment. In a preferred embodiment, theInner Tubular Member 30 is rotated until the travel of the detent is no longer obstructed. The channel in which the detent travels may be of a variety of geometrical shapes such as M, W, L, S Z, etc; the preferred geometry being substantially Z shaped, as shown in FIG. 5. - In an additional embodiment (not shown) of
deployment safety mechanism 118, thedevice 10 has a deployment safety mechanism that comprises male and female locking members that are brought into functional engagement as thestent 12 is being deployed. Once thestent 12 has reached the critical deployment point, the male locking member cannot be advanced further because of a detent formed on the inner diameter of the outer tubular member catches the cavity formed on the corresponding portion of the male locking member. As a result, in order to further advance thedevice 10 to fully deploystent 12, the inner tubular member must be rotated so as to break the detent. Once the detent is broken, the physician will feel a tactile indication that thedevice 10 can be deployed further. - Alternatively, the breaking of the detent may also, or as a substitute to tactile indication, results in an audible indication that further deployment is possible. Additionally, the physician is apprised of the fact that deployment beyond this point is irreversible except for interventional retrieval methods. As discussed earlier, the critical deployment point is preferably about 60% deployment, beyond which retraction is not recommended. As a result, the
safety locking system 60 removes the need to estimate extent of deployment and provides a reliable means of accurately deploying stents. Alternative locking mechanisms may be provided as long as they retain the important characteristic of giving the physician a sensory indication of extent of stent deployment. - The present invention may be embodied in other specific forms without departing from its spirit or essential characteristics. The described embodiments are to be considered in all respects only as illustrative, and not restrictive. The scope of the invention is, therefore, indicated by the appended claims, rather than by the foregoing description. All changes, which come within the meaning and range of equivalency of the claims, are to be embraced within their scope.
Claims (21)
Priority Applications (8)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/281,429 US20040093056A1 (en) | 2002-10-26 | 2002-10-26 | Medical appliance delivery apparatus and method of use |
EP03809965A EP1553903A4 (en) | 2002-10-26 | 2003-10-25 | Medical appliance deployment apparatus and method of use |
CA002503563A CA2503563A1 (en) | 2002-10-26 | 2003-10-25 | Medical appliance deployment apparatus and method of use |
AU2003301732A AU2003301732B2 (en) | 2002-10-26 | 2003-10-25 | Medical appliance deployment apparatus and method of use |
JP2004548493A JP4570957B2 (en) | 2002-10-26 | 2003-10-25 | Medical device delivery device |
PCT/US2003/033967 WO2004039242A2 (en) | 2002-10-26 | 2003-10-25 | Medical appliance deployment apparatus and method of use |
US11/357,366 US7608099B2 (en) | 2002-10-26 | 2006-02-17 | Medical appliance delivery apparatus and method of use |
US12/561,657 US8267987B2 (en) | 2002-10-26 | 2009-09-17 | Medical appliance delivery apparatus and method of use |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/281,429 US20040093056A1 (en) | 2002-10-26 | 2002-10-26 | Medical appliance delivery apparatus and method of use |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/357,366 Continuation US7608099B2 (en) | 2002-10-26 | 2006-02-17 | Medical appliance delivery apparatus and method of use |
Publications (1)
Publication Number | Publication Date |
---|---|
US20040093056A1 true US20040093056A1 (en) | 2004-05-13 |
Family
ID=32228764
Family Applications (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/281,429 Abandoned US20040093056A1 (en) | 2002-10-26 | 2002-10-26 | Medical appliance delivery apparatus and method of use |
US11/357,366 Expired - Lifetime US7608099B2 (en) | 2002-10-26 | 2006-02-17 | Medical appliance delivery apparatus and method of use |
US12/561,657 Expired - Lifetime US8267987B2 (en) | 2002-10-26 | 2009-09-17 | Medical appliance delivery apparatus and method of use |
Family Applications After (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/357,366 Expired - Lifetime US7608099B2 (en) | 2002-10-26 | 2006-02-17 | Medical appliance delivery apparatus and method of use |
US12/561,657 Expired - Lifetime US8267987B2 (en) | 2002-10-26 | 2009-09-17 | Medical appliance delivery apparatus and method of use |
Country Status (6)
Country | Link |
---|---|
US (3) | US20040093056A1 (en) |
EP (1) | EP1553903A4 (en) |
JP (1) | JP4570957B2 (en) |
AU (1) | AU2003301732B2 (en) |
CA (1) | CA2503563A1 (en) |
WO (1) | WO2004039242A2 (en) |
Cited By (24)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20040193243A1 (en) * | 2003-03-31 | 2004-09-30 | Mangiardi Eric K. | Medical appliance optical delivery and deployment apparatus and method |
US20050080476A1 (en) * | 2003-10-09 | 2005-04-14 | Gunderson Richard C. | Medical device delivery system |
US20060253186A1 (en) * | 2005-05-09 | 2006-11-09 | Paragon Intellectual Properties, Llc | Apparatus and methods for renal stenting |
US20060293625A1 (en) * | 2003-12-19 | 2006-12-28 | Hunt John V | Implantable medical device with cover and method |
US20070010790A1 (en) * | 2005-06-24 | 2007-01-11 | Byrum Randal T | Injection port |
US20070100279A1 (en) * | 2005-11-03 | 2007-05-03 | Paragon Intellectual Properties, Llc | Radiopaque-balloon microcatheter and methods of manufacture |
US20070149947A1 (en) * | 2003-12-19 | 2007-06-28 | Byrum Randal T | Audible and tactile feedback |
US20080051867A1 (en) * | 2006-08-28 | 2008-02-28 | Davila Luis A | Multiple in vivo implant delivery device |
US7561916B2 (en) * | 2005-06-24 | 2009-07-14 | Ethicon Endo-Surgery, Inc. | Implantable medical device with indicator |
US20100094257A1 (en) * | 2008-10-10 | 2010-04-15 | Stalker Kent C B | Inventory sparing catheter system |
US20100130941A1 (en) * | 2003-06-16 | 2010-05-27 | Conlon Sean P | Audible And Tactile Feedback |
US7731654B2 (en) | 2005-05-13 | 2010-06-08 | Merit Medical Systems, Inc. | Delivery device with viewing window and associated method |
US20100234808A1 (en) * | 2003-06-16 | 2010-09-16 | Uth Joshua R | Injection Port Applier with Downward Force Actuation |
US7918844B2 (en) | 2005-06-24 | 2011-04-05 | Ethicon Endo-Surgery, Inc. | Applier for implantable medical device |
US20110230899A1 (en) * | 2009-10-23 | 2011-09-22 | Medi-Globe Vascutec Gmbh | Surgical device for feeding at least one suture thread through the edge area of a tissue opening of an individual and method for operating such a device |
US8267987B2 (en) | 2002-10-26 | 2012-09-18 | Merit Medical Systems, Inc. | Medical appliance delivery apparatus and method of use |
US8414635B2 (en) | 1999-02-01 | 2013-04-09 | Idev Technologies, Inc. | Plain woven stents |
US8419788B2 (en) | 2006-10-22 | 2013-04-16 | Idev Technologies, Inc. | Secured strand end devices |
US8876881B2 (en) | 2006-10-22 | 2014-11-04 | Idev Technologies, Inc. | Devices for stent advancement |
US20150025614A1 (en) * | 2008-02-07 | 2015-01-22 | Intuitive Surgical Operations, Inc. | Stent Delivery Under Direct Visualization |
US9023095B2 (en) | 2010-05-27 | 2015-05-05 | Idev Technologies, Inc. | Stent delivery system with pusher assembly |
US10441449B1 (en) | 2018-05-30 | 2019-10-15 | Vesper Medical, Inc. | Rotary handle stent delivery system and method |
US10449073B1 (en) | 2018-09-18 | 2019-10-22 | Vesper Medical, Inc. | Rotary handle stent delivery system and method |
US11219541B2 (en) | 2020-05-21 | 2022-01-11 | Vesper Medical, Inc. | Wheel lock for thumbwheel actuated device |
Families Citing this family (49)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6254564B1 (en) | 1998-09-10 | 2001-07-03 | Percardia, Inc. | Left ventricular conduit with blood vessel graft |
DE102005003632A1 (en) | 2005-01-20 | 2006-08-17 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Catheter for the transvascular implantation of heart valve prostheses |
US8038704B2 (en) | 2005-07-27 | 2011-10-18 | Paul S. Sherburne | Stent and other objects removal from a body |
US7896915B2 (en) | 2007-04-13 | 2011-03-01 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficiency |
US9138315B2 (en) * | 2007-04-13 | 2015-09-22 | Jenavalve Technology Gmbh | Medical device for treating a heart valve insufficiency or stenosis |
JP5220101B2 (en) | 2007-05-15 | 2013-06-26 | イエナバルブ テクノロジー インク | Handle for manipulating the catheter tip, catheter system and medical insertion system to insert a self-expanding heart valve stent |
EP2240121B1 (en) | 2008-01-16 | 2019-05-22 | St. Jude Medical, Inc. | Delivery and retrieval systems for collapsible/expandable prosthetic heart valves |
US9044318B2 (en) | 2008-02-26 | 2015-06-02 | Jenavalve Technology Gmbh | Stent for the positioning and anchoring of a valvular prosthesis |
BR112012021347A2 (en) | 2008-02-26 | 2019-09-24 | Jenavalve Tecnology Inc | stent for positioning and anchoring a valve prosthesis at an implantation site in a patient's heart |
BRPI1008845B8 (en) * | 2009-02-05 | 2021-06-22 | Synthes Gmbh | guide device for drill and chuck |
US9468435B2 (en) | 2009-12-23 | 2016-10-18 | Cook Medical Technologies Llc | Wound closure device |
US8926693B2 (en) * | 2010-02-17 | 2015-01-06 | Medtronic, Inc. | Heart valve delivery catheter with safety button |
KR101135154B1 (en) * | 2010-02-19 | 2012-04-16 | 주식회사 라파스 | Stent delivery devices using micro cadeter |
AU2011257298B2 (en) | 2010-05-25 | 2014-07-31 | Jenavalve Technology Inc. | Prosthetic heart valve and transcatheter delivered endoprosthesis comprising a prosthetic heart valve and a stent |
US20130345787A1 (en) * | 2010-11-29 | 2013-12-26 | Kyoto Medical Planning Co., Ltd. | Medical catheter apparatus |
EP4098226A1 (en) | 2013-08-30 | 2022-12-07 | JenaValve Technology, Inc. | Endoprosthesis comprising a radially collapsible frame and a prosthetic valve |
WO2015038790A1 (en) | 2013-09-12 | 2015-03-19 | Boston Scientific Scimed, Inc. | Stent with anti-migration connectors |
WO2015134500A1 (en) * | 2014-03-03 | 2015-09-11 | Cook Medical Technologies Llc | Mechanical dilator |
ES2678047T3 (en) | 2014-03-18 | 2018-08-08 | Boston Scientific Scimed, Inc. | Stent design to reduce granulation and inflammation |
US10016292B2 (en) | 2014-04-18 | 2018-07-10 | Covidien Lp | Stent delivery system |
AU2015264609B2 (en) | 2014-05-21 | 2017-12-07 | Boston Scientific Scimed, Inc. | Stent delivery system |
WO2016054536A1 (en) | 2014-10-02 | 2016-04-07 | Boston Scientific Scimed, Inc. | Controlled ingrowth feature for antimigration |
EP3485939B1 (en) | 2014-10-22 | 2020-07-15 | Cardiac Pacemakers, Inc. | Delivery devices for leadless cardiac devices |
WO2016065023A1 (en) | 2014-10-22 | 2016-04-28 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
JP2017530811A (en) | 2014-10-22 | 2017-10-19 | ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. | Flexible hinged stent |
WO2016073597A1 (en) | 2014-11-06 | 2016-05-12 | Boston Scientific Scimed, Inc. | Tracheal stent |
EP3288495B1 (en) | 2015-05-01 | 2019-09-25 | JenaValve Technology, Inc. | Device with reduced pacemaker rate in heart valve replacement |
AU2016355676B2 (en) | 2015-11-20 | 2018-12-13 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
CN108348759B (en) | 2015-11-20 | 2021-08-17 | 心脏起搏器股份公司 | Delivery devices and methods for leadless cardiac devices |
EP3454795B1 (en) | 2016-05-13 | 2023-01-11 | JenaValve Technology, Inc. | Heart valve prosthesis delivery system for delivery of heart valve prosthesis with introducer sheath and loading system |
US11198013B2 (en) | 2016-11-21 | 2021-12-14 | Cardiac Pacemakers, Inc. | Catheter and leadless cardiac devices including electrical pathway barrier |
EP3541460B1 (en) | 2016-11-21 | 2020-12-23 | Cardiac Pacemakers, Inc. | Delivery devices and wall apposition sensing |
WO2018136203A1 (en) | 2016-12-27 | 2018-07-26 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
US10806931B2 (en) | 2016-12-27 | 2020-10-20 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
US10485981B2 (en) | 2016-12-27 | 2019-11-26 | Cardiac Pacemakers, Inc. | Fixation methods for leadless cardiac devices |
AU2017387024B2 (en) | 2016-12-27 | 2020-04-09 | Cardiac Pacemakers, Inc. | Leadless delivery catheter with conductive pathway |
CN110225779B (en) | 2017-01-26 | 2023-04-04 | 心脏起搏器股份公司 | Delivery device for leadless cardiac devices |
WO2018138658A1 (en) | 2017-01-27 | 2018-08-02 | Jenavalve Technology, Inc. | Heart valve mimicry |
CN110418661B (en) | 2017-03-10 | 2024-01-02 | 心脏起搏器股份公司 | Fixing piece for leadless cardiac device |
US10737092B2 (en) | 2017-03-30 | 2020-08-11 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
US11577085B2 (en) | 2017-08-03 | 2023-02-14 | Cardiac Pacemakers, Inc. | Delivery devices and methods for leadless cardiac devices |
US11083609B2 (en) * | 2018-04-24 | 2021-08-10 | Medtronic Vascular, Inc. | Selectable tip delivery system and method |
CN113660977A (en) | 2019-03-29 | 2021-11-16 | 心脏起搏器股份公司 | System and method for treating cardiac arrhythmias |
US11446510B2 (en) | 2019-03-29 | 2022-09-20 | Cardiac Pacemakers, Inc. | Systems and methods for treating cardiac arrhythmias |
KR102244846B1 (en) * | 2019-04-18 | 2021-04-28 | 주식회사 엠아이텍 | Stent delivery device |
WO2020263742A1 (en) * | 2019-06-24 | 2020-12-30 | Medtronic, Inc. | Catheter handle with torque mechanism and valve relief component |
WO2021050679A1 (en) | 2019-09-11 | 2021-03-18 | Cardiac Pacemakers, Inc. | Tools and systems for implanting and/or retrieving a leadless cardiac pacing device with helix fixation |
WO2021050685A1 (en) | 2019-09-11 | 2021-03-18 | Cardiac Pacemakers, Inc. | Tools and systems for implanting and/or retrieving a leadless cardiac pacing device with helix fixation |
WO2021146021A1 (en) | 2020-01-13 | 2021-07-22 | Boston Scientific Scimed, Inc. | Anti-migration stent |
Citations (82)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3196876A (en) * | 1961-05-10 | 1965-07-27 | Maurice M Miller | Dilator |
US4606330A (en) * | 1983-08-09 | 1986-08-19 | Richard Wolf Gmbh | Device for disintegrating stones in bodily cavities or ducts |
US4893623A (en) * | 1986-12-09 | 1990-01-16 | Advanced Surgical Intervention, Inc. | Method and apparatus for treating hypertrophy of the prostate gland |
US5019085A (en) * | 1988-10-25 | 1991-05-28 | Cordis Corporation | Apparatus and method for placement of a stent within a subject vessel |
US5159920A (en) * | 1990-06-18 | 1992-11-03 | Mentor Corporation | Scope and stent system |
US5249585A (en) * | 1988-07-28 | 1993-10-05 | Bsd Medical Corporation | Urethral inserted applicator for prostate hyperthermia |
US5302906A (en) * | 1990-03-21 | 1994-04-12 | Siemens Aktiengesellschaft | Method and arrangement for determining a load angle of a generator which is connected to an electrical supply network |
US5320617A (en) * | 1993-06-25 | 1994-06-14 | Leach Gary E | Method of laser-assisted prostatectomy and apparatus for carrying out the method |
US5409453A (en) * | 1992-08-12 | 1995-04-25 | Vidamed, Inc. | Steerable medical probe with stylets |
US5433723A (en) * | 1991-10-11 | 1995-07-18 | Angiomed Ag | Apparatus for widening a stenosis |
US5514093A (en) * | 1994-05-19 | 1996-05-07 | Scimed Life Systems, Inc. | Variable length balloon dilatation catheter |
US5549644A (en) * | 1992-08-12 | 1996-08-27 | Vidamed, Inc. | Transurethral needle ablation device with cystoscope and method for treatment of the prostate |
US5565211A (en) * | 1993-06-22 | 1996-10-15 | Crina S.A. | Composition for improving the digestibility of feed intended for ruminants |
US5588949A (en) * | 1993-10-08 | 1996-12-31 | Heartport, Inc. | Stereoscopic percutaneous visualization system |
US5601591A (en) * | 1994-09-23 | 1997-02-11 | Vidamed, Inc. | Stent for use in prostatic urethra, apparatus and placement device for same and method |
US5603698A (en) * | 1993-04-13 | 1997-02-18 | Boston Scientific Corporation | Prosthesis delivery system |
US5667522A (en) * | 1994-03-03 | 1997-09-16 | Medinol Ltd. | Urological stent and deployment device therefor |
US5690644A (en) * | 1992-12-30 | 1997-11-25 | Schneider (Usa) Inc. | Apparatus for deploying body implantable stent |
US5746692A (en) * | 1994-05-05 | 1998-05-05 | Imagen Medical, Inc. | Catheter and endoscope system with distal protruding ball tip and method |
US5782838A (en) * | 1994-10-20 | 1998-07-21 | Medtronic Instent, Inc. | Cytoscope delivery system |
US5803080A (en) * | 1995-12-20 | 1998-09-08 | Willy Rusch Ag | Instrument for interventional flexible tracheoscopy/bronchoscopy |
US5817102A (en) * | 1992-05-08 | 1998-10-06 | Schneider (Usa) Inc. | Apparatus for delivering and deploying a stent |
US5824058A (en) * | 1993-05-20 | 1998-10-20 | Boston Scientific Corporation | Prosthesis delivery |
US5833694A (en) * | 1995-05-25 | 1998-11-10 | Medtronic, Inc. | Stent assembly and method of use |
US5902333A (en) * | 1993-04-13 | 1999-05-11 | Boston Scientific Corporation | Prosthesis delivery system with dilating tip |
US5968052A (en) * | 1996-11-27 | 1999-10-19 | Scimed Life Systems Inc. | Pull back stent delivery system with pistol grip retraction handle |
US6019778A (en) * | 1998-03-13 | 2000-02-01 | Cordis Corporation | Delivery apparatus for a self-expanding stent |
US6086528A (en) * | 1997-09-11 | 2000-07-11 | Adair; Edwin L. | Surgical devices with removable imaging capability and methods of employing same |
US6162231A (en) * | 1998-09-14 | 2000-12-19 | Endocare, Inc. | Stent insertion device |
US6203550B1 (en) * | 1998-09-30 | 2001-03-20 | Medtronic, Inc. | Disposable delivery device for endoluminal prostheses |
US6322586B1 (en) * | 2000-01-10 | 2001-11-27 | Scimed Life Systems, Inc. | Catheter tip designs and method of manufacture |
US6325790B1 (en) * | 1995-04-11 | 2001-12-04 | Cordis Corporation | Soft tip catheter |
US6369355B1 (en) * | 1994-11-28 | 2002-04-09 | Advance Cardiovascular Systems, Inc. | Method and apparatus for direct laser cutting of metal stents |
US6375676B1 (en) * | 1999-05-17 | 2002-04-23 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent with enhanced delivery precision and stent delivery system |
US6451025B1 (en) * | 1996-04-01 | 2002-09-17 | General Surgical Innovations, Inc. | Prosthesis and method for deployment within a body lumen |
US20020161425A1 (en) * | 2001-04-30 | 2002-10-31 | Scimed Life Systems, Inc. | Endoscopic stent delivery system and method |
US20020183763A1 (en) * | 2001-05-17 | 2002-12-05 | Callol Joseph R. | Stent and catheter assembly and method for treating bifurcations |
US6517569B2 (en) * | 1998-09-14 | 2003-02-11 | Endocare, Inc. | Insertion device for stents and methods for use |
US20030074045A1 (en) * | 2001-10-12 | 2003-04-17 | Jon Buzzard | Locking handle deployment mechanism for medical device and method |
US6569085B2 (en) * | 2001-08-16 | 2003-05-27 | Syntheon, Llc | Methods and apparatus for delivering a medical instrument over an endoscope while the endoscope is in a body lumen |
US20030144671A1 (en) * | 1998-09-30 | 2003-07-31 | Brooks Christopher J. | Delivery mechanism for implantable stents-grafts |
US6623491B2 (en) * | 2001-01-18 | 2003-09-23 | Ev3 Peripheral, Inc. | Stent delivery system with spacer member |
US6656214B1 (en) * | 1995-09-08 | 2003-12-02 | Medtronic Ave, Inc. | Methods and apparatus for conformably sealing prostheses within body lumens |
US6663660B2 (en) * | 1996-08-23 | 2003-12-16 | Scimed Life Systems, Inc. | Stent delivery system having stent securement apparatus |
US6663880B1 (en) * | 2001-11-30 | 2003-12-16 | Advanced Cardiovascular Systems, Inc. | Permeabilizing reagents to increase drug delivery and a method of local delivery |
US6669716B1 (en) * | 1998-03-31 | 2003-12-30 | Salviac Limited | Delivery catheter |
US6669718B2 (en) * | 1999-11-18 | 2003-12-30 | Petrus Besselink | Apparatus and method for placing bifurcated stents |
US6669720B1 (en) * | 1997-01-28 | 2003-12-30 | George E. Pierce | Prosthesis for endovascular repair of abdominal aortic aneurysms |
US6673101B1 (en) * | 2002-10-09 | 2004-01-06 | Endovascular Technologies, Inc. | Apparatus and method for deploying self-expanding stents |
US20040006380A1 (en) * | 2002-07-05 | 2004-01-08 | Buck Jerrick C. | Stent delivery system |
US6676693B1 (en) * | 2001-06-27 | 2004-01-13 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for delivering a self-expanding stent |
US6676692B2 (en) * | 2001-04-27 | 2004-01-13 | Intek Technology L.L.C. | Apparatus for delivering, repositioning and/or retrieving self-expanding stents |
US6689157B2 (en) * | 1999-07-07 | 2004-02-10 | Endologix, Inc. | Dual wire placement catheter |
US6695812B2 (en) * | 1999-06-30 | 2004-02-24 | Advanced Cardiovascular Systems, Inc. | Catheter with enhanced flexibility |
US6695809B1 (en) * | 1999-09-13 | 2004-02-24 | Advanced Cardiovascular Systems, Inc. | Catheter balloon with a discontinuous elastomeric outer layer |
US6699277B1 (en) * | 2000-03-09 | 2004-03-02 | Diseno Y Desarrollo Medica, S.A. De C.V. | Stent with cover connectors |
US6699274B2 (en) * | 2001-01-22 | 2004-03-02 | Scimed Life Systems, Inc. | Stent delivery system and method of manufacturing same |
US6702850B1 (en) * | 2002-09-30 | 2004-03-09 | Mediplex Corporation Korea | Multi-coated drug-eluting stent for antithrombosis and antirestenosis |
US6702849B1 (en) * | 1999-12-13 | 2004-03-09 | Advanced Cardiovascular Systems, Inc. | Method of processing open-celled microcellular polymeric foams with controlled porosity for use as vascular grafts and stent covers |
US6723113B1 (en) * | 2000-01-19 | 2004-04-20 | Cordis Neurovascular, Inc. | Inflatable balloon catheter seal and method |
US6723071B2 (en) * | 2001-03-14 | 2004-04-20 | Scimed Life Systems, Inc. | Rapid exchange stent delivery system and associated components |
US6726712B1 (en) * | 1999-05-14 | 2004-04-27 | Boston Scientific Scimed | Prosthesis deployment device with translucent distal end |
US6733521B2 (en) * | 2001-04-11 | 2004-05-11 | Trivascular, Inc. | Delivery system and method for endovascular graft |
US6736828B1 (en) * | 2000-09-29 | 2004-05-18 | Scimed Life Systems, Inc. | Method for performing endoluminal fundoplication and apparatus for use in the method |
US6743219B1 (en) * | 2000-08-02 | 2004-06-01 | Cordis Corporation | Delivery apparatus for a self-expanding stent |
US6746423B1 (en) * | 2001-11-01 | 2004-06-08 | Advanced Cardiovascular Systems, Inc. | Catheter having improved rapid exchange junction |
US6749627B2 (en) * | 2001-01-18 | 2004-06-15 | Ev3 Peripheral, Inc. | Grip for stent delivery system |
US6752819B1 (en) * | 1998-04-02 | 2004-06-22 | Salviac Limited | Delivery catheter |
US6752825B2 (en) * | 2001-10-02 | 2004-06-22 | Scimed Life Systems, Inc | Nested stent apparatus |
US6761703B2 (en) * | 2001-07-03 | 2004-07-13 | Scimed Life Systems, Inc. | Catheter incorporating a high column high column strength distal tip region |
US6761708B1 (en) * | 2000-10-31 | 2004-07-13 | Advanced Cardiovascular Systems, Inc. | Radiopaque marker for a catheter and method of making |
US6761733B2 (en) * | 2001-04-11 | 2004-07-13 | Trivascular, Inc. | Delivery system and method for bifurcated endovascular graft |
US6773447B2 (en) * | 2002-07-02 | 2004-08-10 | Sentient Engineering & Technology, Llc | Balloon catheter and treatment apparatus |
US6773448B2 (en) * | 2002-03-08 | 2004-08-10 | Ev3 Inc. | Distal protection devices having controllable wire motion |
US6780182B2 (en) * | 2002-05-23 | 2004-08-24 | Adiana, Inc. | Catheter placement detection system and operator interface |
US6780199B2 (en) * | 1998-05-15 | 2004-08-24 | Advanced Cardiovascular Systems, Inc. | Enhanced stent delivery system |
US6790223B2 (en) * | 2001-09-21 | 2004-09-14 | Scimed Life Systems, Inc. | Delivering a uretheral stent |
US6790220B2 (en) * | 2001-06-08 | 2004-09-14 | Morris Innovative Research, Inc. | Method and apparatus for sealing access |
US6800081B2 (en) * | 1998-09-18 | 2004-10-05 | Aptus Endosystems, Inc. | Systems and methods for applying a suture within a blood vesel lumen |
US6802846B2 (en) * | 2001-02-12 | 2004-10-12 | Ams Research Corporation | Foreign body retrieval device and method |
US6802849B2 (en) * | 1996-08-23 | 2004-10-12 | Scimed Life Systems, Inc. | Stent delivery system |
US6808529B2 (en) * | 2000-02-11 | 2004-10-26 | Edwards Lifesciences Corporation | Apparatus and methods for delivery of intraluminal prostheses |
Family Cites Families (249)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB2056023B (en) | 1979-08-06 | 1983-08-10 | Ross D N Bodnar E | Stent for a cardiac valve |
US4680031A (en) | 1982-11-29 | 1987-07-14 | Tascon Medical Technology Corporation | Heart valve prosthesis |
US5067957A (en) | 1983-10-14 | 1991-11-26 | Raychem Corporation | Method of inserting medical devices incorporating SIM alloy elements |
US4665906A (en) | 1983-10-14 | 1987-05-19 | Raychem Corporation | Medical devices incorporating sim alloy elements |
US5190546A (en) * | 1983-10-14 | 1993-03-02 | Raychem Corporation | Medical devices incorporating SIM alloy elements |
US4733665C2 (en) * | 1985-11-07 | 2002-01-29 | Expandable Grafts Partnership | Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft |
US5102417A (en) * | 1985-11-07 | 1992-04-07 | Expandable Grafts Partnership | Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft |
US4820262A (en) * | 1985-12-12 | 1989-04-11 | Medical Engineering Corporation | Ureteral stent |
US5032128A (en) | 1988-07-07 | 1991-07-16 | Medtronic, Inc. | Heart valve prosthesis |
SE8803444D0 (en) * | 1988-09-28 | 1988-09-28 | Medinvent Sa | A DEVICE FOR TRANSLUMINAL IMPLANTATION OR EXTRACTION |
CA1322628C (en) * | 1988-10-04 | 1993-10-05 | Richard A. Schatz | Expandable intraluminal graft |
US4957479A (en) | 1988-10-17 | 1990-09-18 | Vance Products Incorporated | Indwelling ureteral stent placement apparatus |
US4856516A (en) | 1989-01-09 | 1989-08-15 | Cordis Corporation | Endovascular stent apparatus and method |
US5292331A (en) * | 1989-08-24 | 1994-03-08 | Applied Vascular Engineering, Inc. | Endovascular support device |
IE73670B1 (en) * | 1989-10-02 | 1997-07-02 | Medtronic Inc | Articulated stent |
US5469854A (en) | 1989-12-22 | 1995-11-28 | Imarx Pharmaceutical Corp. | Methods of preparing gas-filled liposomes |
US5356423A (en) | 1991-01-04 | 1994-10-18 | American Medical Systems, Inc. | Resectable self-expanding stent |
US5073694A (en) | 1991-02-21 | 1991-12-17 | Synthes (U.S.A.) | Method and apparatus for laser cutting a hollow metal workpiece |
US5591172A (en) | 1991-06-14 | 1997-01-07 | Ams Medinvent S.A. | Transluminal implantation device |
US6029671A (en) | 1991-07-16 | 2000-02-29 | Heartport, Inc. | System and methods for performing endovascular procedures |
US5443498A (en) | 1991-10-01 | 1995-08-22 | Cook Incorporated | Vascular stent and method of making and implanting a vacsular stent |
US5876445A (en) * | 1991-10-09 | 1999-03-02 | Boston Scientific Corporation | Medical stents for body lumens exhibiting peristaltic motion |
US5662713A (en) | 1991-10-09 | 1997-09-02 | Boston Scientific Corporation | Medical stents for body lumens exhibiting peristaltic motion |
US5354309A (en) | 1991-10-11 | 1994-10-11 | Angiomed Ag | Apparatus for widening a stenosis in a body cavity |
CA2380683C (en) | 1991-10-28 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Expandable stents and method for making same |
FR2683449A1 (en) * | 1991-11-08 | 1993-05-14 | Cardon Alain | ENDOPROTHESIS FOR TRANSLUMINAL IMPLANTATION. |
US5201757A (en) | 1992-04-03 | 1993-04-13 | Schneider (Usa) Inc. | Medial region deployment of radially self-expanding stents |
DE9390115U1 (en) * | 1992-05-08 | 1994-12-22 | Schneider Usa Inc | Esophageal stent and delivery instrument |
DE4303181A1 (en) * | 1993-02-04 | 1994-08-11 | Angiomed Ag | Implantable catheter |
EP1163890B1 (en) | 1993-03-11 | 2005-08-10 | Medinol Ltd. | Stent |
CA2092497C (en) | 1993-03-25 | 1997-03-25 | Fritz Muller | Method of cutting an aperture in a device by means of a laser beam |
EP0621015B1 (en) | 1993-04-23 | 1998-03-18 | Schneider (Europe) Ag | Stent with a covering layer of elastic material and method for applying the layer on the stent |
US6685736B1 (en) * | 1993-09-30 | 2004-02-03 | Endogad Research Pty Limited | Intraluminal graft |
DE69419877T2 (en) | 1993-11-04 | 1999-12-16 | Bard Inc C R | Fixed vascular prosthesis |
RU2089131C1 (en) | 1993-12-28 | 1997-09-10 | Сергей Апполонович Пульнев | Stent-expander |
US5609627A (en) | 1994-02-09 | 1997-03-11 | Boston Scientific Technology, Inc. | Method for delivering a bifurcated endoluminal prosthesis |
US5443477A (en) * | 1994-02-10 | 1995-08-22 | Stentco, Inc. | Apparatus and method for deployment of radially expandable stents by a mechanical linkage |
US5643312A (en) | 1994-02-25 | 1997-07-01 | Fischell Robert | Stent having a multiplicity of closed circular structures |
SI0669114T1 (en) | 1994-02-25 | 1999-02-28 | Robert E. Fischell | Stent having a multiplicity of closed circular structures |
US5843120A (en) | 1994-03-17 | 1998-12-01 | Medinol Ltd. | Flexible-expandable stent |
US5733303A (en) * | 1994-03-17 | 1998-03-31 | Medinol Ltd. | Flexible expandable stent |
US5449373A (en) | 1994-03-17 | 1995-09-12 | Medinol Ltd. | Articulated stent |
US6464722B2 (en) | 1994-03-17 | 2002-10-15 | Medinol, Ltd. | Flexible expandable stent |
US6461381B2 (en) | 1994-03-17 | 2002-10-08 | Medinol, Ltd. | Flexible expandable stent |
DE4418336A1 (en) * | 1994-05-26 | 1995-11-30 | Angiomed Ag | Stent for widening and holding open receptacles |
EP0792627B2 (en) | 1994-06-08 | 2003-10-29 | Cardiovascular Concepts, Inc. | System for forming a bifurcated graft |
US5683451A (en) | 1994-06-08 | 1997-11-04 | Cardiovascular Concepts, Inc. | Apparatus and methods for deployment release of intraluminal prostheses |
US5591157A (en) * | 1994-09-07 | 1997-01-07 | Hennings; David R. | Method and apparatus for tympanic membrane shrinkage |
AU708360B2 (en) | 1994-09-15 | 1999-08-05 | C.R. Bard Inc. | Hooked endoprosthesis |
US6746482B2 (en) | 1994-10-17 | 2004-06-08 | Baxter International Inc. | Method for producing medical devices and devices so produced |
DE69519387T2 (en) | 1994-10-27 | 2001-03-15 | Boston Scient Ltd | INSTRUMENT FOR ATTACHING A STENT |
US5836964A (en) | 1996-10-30 | 1998-11-17 | Medinol Ltd. | Stent fabrication method |
CA2134997C (en) | 1994-11-03 | 2009-06-02 | Ian M. Penn | Stent |
DE4446036C2 (en) | 1994-12-23 | 1999-06-02 | Ruesch Willy Ag | Placeholder for placement in a body tube |
AU719980B2 (en) | 1995-02-22 | 2000-05-18 | Menlo Care, Inc. | Covered expanding mesh stent |
US7204848B1 (en) | 1995-03-01 | 2007-04-17 | Boston Scientific Scimed, Inc. | Longitudinally flexible expandable stent |
DE19508805C2 (en) * | 1995-03-06 | 2000-03-30 | Lutz Freitag | Stent for placement in a body tube with a flexible support structure made of at least two wires with different shape memory functions |
US6451047B2 (en) | 1995-03-10 | 2002-09-17 | Impra, Inc. | Encapsulated intraluminal stent-graft and methods of making same |
US6579314B1 (en) | 1995-03-10 | 2003-06-17 | C.R. Bard, Inc. | Covered stent with encapsulated ends |
US5591197A (en) | 1995-03-14 | 1997-01-07 | Advanced Cardiovascular Systems, Inc. | Expandable stent forming projecting barbs and method for deploying |
ATE169484T1 (en) * | 1995-04-01 | 1998-08-15 | Variomed Ag | STENT FOR TRANSLUMINAL IMPLANTATION IN HOLLOW ORGANS |
BE1009278A3 (en) * | 1995-04-12 | 1997-01-07 | Corvita Europ | Guardian self-expandable medical device introduced in cavite body, and medical device with a stake as. |
US5837313A (en) | 1995-04-19 | 1998-11-17 | Schneider (Usa) Inc | Drug release stent coating process |
US5593442A (en) * | 1995-06-05 | 1997-01-14 | Localmed, Inc. | Radially expansible and articulated vessel scaffold |
US6774278B1 (en) | 1995-06-07 | 2004-08-10 | Cook Incorporated | Coated implantable medical device |
CA2178541C (en) * | 1995-06-07 | 2009-11-24 | Neal E. Fearnot | Implantable medical device |
US5609629A (en) * | 1995-06-07 | 1997-03-11 | Med Institute, Inc. | Coated implantable medical device |
US5702418A (en) * | 1995-09-12 | 1997-12-30 | Boston Scientific Corporation | Stent delivery system |
US5776161A (en) | 1995-10-16 | 1998-07-07 | Instent, Inc. | Medical stents, apparatus and method for making same |
US6428538B1 (en) * | 1995-10-20 | 2002-08-06 | United States Surgical Corporation | Apparatus and method for thermal treatment of body tissue |
US5628788A (en) | 1995-11-07 | 1997-05-13 | Corvita Corporation | Self-expanding endoluminal stent-graft |
US6719782B1 (en) | 1996-01-04 | 2004-04-13 | Endovascular Technologies, Inc. | Flat wire stent |
EP0879068A4 (en) | 1996-02-02 | 1999-04-21 | Transvascular Inc | Methods and apparatus for blocking flow through blood vessels |
CA2248718A1 (en) | 1996-03-05 | 1997-09-12 | Divysio Solutions Ulc. | Expandable stent and method for delivery of same |
CA2192520A1 (en) * | 1996-03-05 | 1997-09-05 | Ian M. Penn | Expandable stent and method for delivery of same |
US6796997B1 (en) | 1996-03-05 | 2004-09-28 | Evysio Medical Devices Ulc | Expandable stent |
CA2199890C (en) | 1996-03-26 | 2002-02-05 | Leonard Pinchuk | Stents and stent-grafts having enhanced hoop strength and methods of making the same |
US5824042A (en) | 1996-04-05 | 1998-10-20 | Medtronic, Inc. | Endoluminal prostheses having position indicating markers |
US5713949A (en) * | 1996-08-06 | 1998-02-03 | Jayaraman; Swaminathan | Microporous covered stents and method of coating |
US6629981B2 (en) * | 2000-07-06 | 2003-10-07 | Endocare, Inc. | Stent delivery system |
US5830179A (en) | 1996-04-09 | 1998-11-03 | Endocare, Inc. | Urological stent therapy system and method |
JP4636634B2 (en) | 1996-04-26 | 2011-02-23 | ボストン サイエンティフィック サイムド,インコーポレイテッド | Intravascular stent |
UA58485C2 (en) | 1996-05-03 | 2003-08-15 | Медінол Лтд. | Method for manufacture of bifurcated stent (variants) and bifurcated stent (variants) |
US6251133B1 (en) | 1996-05-03 | 2001-06-26 | Medinol Ltd. | Bifurcated stent with improved side branch aperture and method of making same |
IL122904A0 (en) | 1996-05-31 | 1998-08-16 | Bard Galway Ltd | Bifurcated endovascular stents and method and apparatus for their placement |
US8728143B2 (en) | 1996-06-06 | 2014-05-20 | Biosensors International Group, Ltd. | Endoprosthesis deployment system for treating vascular bifurcations |
US5776140A (en) * | 1996-07-16 | 1998-07-07 | Cordis Corporation | Stent delivery system |
US5922020A (en) | 1996-08-02 | 1999-07-13 | Localmed, Inc. | Tubular prosthesis having improved expansion and imaging characteristics |
US6174329B1 (en) | 1996-08-22 | 2001-01-16 | Advanced Cardiovascular Systems, Inc. | Protective coating for a stent with intermediate radiopaque coating |
US5797887A (en) | 1996-08-27 | 1998-08-25 | Novovasc Llc | Medical device with a surface adapted for exposure to a blood stream which is coated with a polymer containing a nitrosyl-containing organo-metallic compound which releases nitric oxide from the coating to mediate platelet aggregation |
US5807404A (en) | 1996-09-19 | 1998-09-15 | Medinol Ltd. | Stent with variable features to optimize support and method of making such stent |
ATE309762T1 (en) * | 1996-09-26 | 2005-12-15 | Scimed Life Systems Inc | COMBINED MEDICAL DEVICE CONSISTING OF A SUPPORT STRUCTURE AND A MEMBRANE |
US5755776A (en) | 1996-10-04 | 1998-05-26 | Al-Saadon; Khalid | Permanent expandable intraluminal tubular stent |
US5868781A (en) * | 1996-10-22 | 1999-02-09 | Scimed Life Systems, Inc. | Locking stent |
US6325826B1 (en) * | 1998-01-14 | 2001-12-04 | Advanced Stent Technologies, Inc. | Extendible stent apparatus |
US6692483B2 (en) * | 1996-11-04 | 2004-02-17 | Advanced Stent Technologies, Inc. | Catheter with attached flexible side sheath |
WO1998020810A1 (en) | 1996-11-12 | 1998-05-22 | Medtronic, Inc. | Flexible, radially expansible luminal prostheses |
US6395017B1 (en) | 1996-11-15 | 2002-05-28 | C. R. Bard, Inc. | Endoprosthesis delivery catheter with sequential stage control |
JP2001506146A (en) | 1996-12-13 | 2001-05-15 | データ サイエスシズ インターナショナル,インコーポレイティド | Biocompatible medical device with polyurethane surface |
US5868782A (en) | 1996-12-24 | 1999-02-09 | Global Therapeutics, Inc. | Radially expandable axially non-contracting surgical stent |
US5906759A (en) * | 1996-12-26 | 1999-05-25 | Medinol Ltd. | Stent forming apparatus with stent deforming blades |
IT1289815B1 (en) | 1996-12-30 | 1998-10-16 | Sorin Biomedica Cardio Spa | ANGIOPLASTIC STENT AND RELATED PRODUCTION PROCESS |
US5876400A (en) | 1997-01-13 | 1999-03-02 | Pioneer Laboratories, Inc. | Electrocautery method and apparatus |
US5827321A (en) | 1997-02-07 | 1998-10-27 | Cornerstone Devices, Inc. | Non-Foreshortening intraluminal prosthesis |
US5911732A (en) | 1997-03-10 | 1999-06-15 | Johnson & Johnson Interventional Systems, Co. | Articulated expandable intraluminal stent |
US5902475A (en) | 1997-04-08 | 1999-05-11 | Interventional Technologies, Inc. | Method for manufacturing a stent |
US6240616B1 (en) | 1997-04-15 | 2001-06-05 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing a medicated porous metal prosthesis |
US6776792B1 (en) | 1997-04-24 | 2004-08-17 | Advanced Cardiovascular Systems Inc. | Coated endovascular stent |
US6033433A (en) | 1997-04-25 | 2000-03-07 | Scimed Life Systems, Inc. | Stent configurations including spirals |
US6451049B2 (en) | 1998-04-29 | 2002-09-17 | Sorin Biomedica Cardio, S.P.A. | Stents for angioplasty |
DE19718339A1 (en) * | 1997-04-30 | 1998-11-12 | Schering Ag | Polymer coated stents, processes for their manufacture and their use for restenosis prophylaxis |
DE29708803U1 (en) * | 1997-05-17 | 1997-07-31 | Jomed Implantate Gmbh | Radially expandable stent for implantation in a body vessel in the area of a vascular branch |
DE29708879U1 (en) * | 1997-05-20 | 1997-07-31 | Jomed Implantate Gmbh | Coronary stent |
US5836966A (en) | 1997-05-22 | 1998-11-17 | Scimed Life Systems, Inc. | Variable expansion force stent |
BE1011180A6 (en) * | 1997-05-27 | 1999-06-01 | Medicorp R & D Benelux Sa | Luminal endoprosthesis AUTO EXPANDABLE. |
US6723121B1 (en) | 1997-06-18 | 2004-04-20 | Scimed Life Systems, Inc. | Polycarbonate-polyurethane dispersions for thrombo-resistant coatings |
US6165195A (en) | 1997-08-13 | 2000-12-26 | Advanced Cardiovascylar Systems, Inc. | Stent and catheter assembly and method for treating bifurcations |
US6316522B1 (en) | 1997-08-18 | 2001-11-13 | Scimed Life Systems, Inc. | Bioresorbable hydrogel compositions for implantable prostheses |
US6746476B1 (en) | 1997-09-22 | 2004-06-08 | Cordis Corporation | Bifurcated axially flexible stent |
US6231598B1 (en) | 1997-09-24 | 2001-05-15 | Med Institute, Inc. | Radially expandable stent |
DE29718773U1 (en) * | 1997-10-22 | 1997-12-04 | Stocko Metallwarenfab Henkels | Chip card contact unit |
US6033435A (en) * | 1997-11-03 | 2000-03-07 | Divysio Solutions Ulc | Bifurcated stent and method for the manufacture and delivery of same |
NO311781B1 (en) | 1997-11-13 | 2002-01-28 | Medinol Ltd | Metal multilayer stents |
US6330884B1 (en) | 1997-11-14 | 2001-12-18 | Transvascular, Inc. | Deformable scaffolding multicellular stent |
US6179867B1 (en) * | 1998-01-16 | 2001-01-30 | Advanced Cardiovascular Systems, Inc. | Flexible stent and method of use |
EP0945107A3 (en) | 1998-01-23 | 2000-01-19 | Arterial Vascular Engineering, Inc. | Helical stent |
US6533807B2 (en) | 1998-02-05 | 2003-03-18 | Medtronic, Inc. | Radially-expandable stent and delivery system |
US6488701B1 (en) * | 1998-03-31 | 2002-12-03 | Medtronic Ave, Inc. | Stent-graft assembly with thin-walled graft component and method of manufacture |
US5938697A (en) | 1998-03-04 | 1999-08-17 | Scimed Life Systems, Inc. | Stent having variable properties |
DE69942666D1 (en) | 1998-03-05 | 2010-09-23 | Boston Scient Ltd | INTRALUMINAL STENT |
US5935162A (en) | 1998-03-16 | 1999-08-10 | Medtronic, Inc. | Wire-tubular hybrid stent |
US6132461A (en) | 1998-03-27 | 2000-10-17 | Intratherapeutics, Inc. | Stent with dual support structure |
EP1076534B1 (en) | 1998-05-05 | 2007-04-04 | Boston Scientific Limited | Stent with smooth ends |
DE19822157B4 (en) | 1998-05-16 | 2013-01-10 | Abbott Laboratories Vascular Enterprises Ltd. | Radially expandable stent for implantation in a body vessel |
US6740113B2 (en) | 1998-05-29 | 2004-05-25 | Scimed Life Systems, Inc. | Balloon expandable stent with a self-expanding portion |
AU756080B2 (en) | 1998-06-04 | 2003-01-02 | New York University | Endovascular thin film devices and methods for treating and preventing stroke |
WO2000010622A1 (en) | 1998-08-20 | 2000-03-02 | Cook Incorporated | Coated implantable medical device |
US6193744B1 (en) | 1998-09-10 | 2001-02-27 | Scimed Life Systems, Inc. | Stent configurations |
US6432126B1 (en) | 1998-09-30 | 2002-08-13 | C.R. Bard, Inc. | Flexible vascular inducing implants |
US6042597A (en) * | 1998-10-23 | 2000-03-28 | Scimed Life Systems, Inc. | Helical stent design |
US6475234B1 (en) | 1998-10-26 | 2002-11-05 | Medinol, Ltd. | Balloon expandable covered stents |
AU1085800A (en) | 1998-11-11 | 2000-05-29 | Mark Wilson Ian Webster | Bifurcation stent and delivery systems |
US6733523B2 (en) | 1998-12-11 | 2004-05-11 | Endologix, Inc. | Implantable vascular graft |
US6660030B2 (en) | 1998-12-11 | 2003-12-09 | Endologix, Inc. | Bifurcation graft deployment catheter |
US6383204B1 (en) | 1998-12-15 | 2002-05-07 | Micrus Corporation | Variable stiffness coil for vasoocclusive devices |
US6530950B1 (en) | 1999-01-12 | 2003-03-11 | Quanam Medical Corporation | Intraluminal stent having coaxial polymer member |
US6454789B1 (en) | 1999-01-15 | 2002-09-24 | Light Science Corporation | Patient portable device for photodynamic therapy |
US6673102B1 (en) * | 1999-01-22 | 2004-01-06 | Gore Enterprises Holdings, Inc. | Covered endoprosthesis and delivery system |
US6361557B1 (en) * | 1999-02-05 | 2002-03-26 | Medtronic Ave, Inc. | Staplebutton radiopaque marker |
US6695876B1 (en) * | 1999-02-12 | 2004-02-24 | Thomas R. Marotta | Endovascular prosthesis |
DE19906956B4 (en) | 1999-02-19 | 2011-07-21 | QualiMed Innovative Medizin-Produkte GmbH, 21423 | Stent and method for producing a stent |
US6514245B1 (en) * | 1999-03-15 | 2003-02-04 | Cryovascular Systems, Inc. | Safety cryotherapy catheter |
US6248122B1 (en) | 1999-02-26 | 2001-06-19 | Vascular Architects, Inc. | Catheter with controlled release endoluminal prosthesis |
US6364903B2 (en) | 1999-03-19 | 2002-04-02 | Meadox Medicals, Inc. | Polymer coated stent |
WO2000062711A1 (en) | 1999-04-15 | 2000-10-26 | Smart Therapeutics, Inc. | Intravascular stent and method of treating neurovascualr vessel lesion |
US6730116B1 (en) | 1999-04-16 | 2004-05-04 | Medtronic, Inc. | Medical device for intraluminal endovascular stenting |
US6673103B1 (en) * | 1999-05-20 | 2004-01-06 | Scimed Life Systems, Inc. | Mesh and stent for increased flexibility |
CA2371780C (en) | 1999-05-20 | 2009-10-06 | Boston Scientific Limited | Stent delivery system with nested stabilizer and method of loading and using same |
US6398802B1 (en) | 1999-06-21 | 2002-06-04 | Scimed Life Systems, Inc. | Low profile delivery system for stent and graft deployment |
US6488697B1 (en) | 1999-07-13 | 2002-12-03 | Terumo Kabushiki Kaisha | Apparatus for thermotherapy |
DE19937638B4 (en) | 1999-08-12 | 2006-11-02 | Alveolus Inc. | Tracheal Stent |
KR100341019B1 (en) | 1999-08-18 | 2002-06-20 | 신경민 | The flexible self- expandable stent foundation device |
US6299622B1 (en) | 1999-08-19 | 2001-10-09 | Fox Hollow Technologies, Inc. | Atherectomy catheter with aligned imager |
US6790228B2 (en) | 1999-12-23 | 2004-09-14 | Advanced Cardiovascular Systems, Inc. | Coating for implantable devices and a method of forming the same |
US6383213B2 (en) | 1999-10-05 | 2002-05-07 | Advanced Cardiovascular Systems, Inc. | Stent and catheter assembly and method for treating bifurcations |
US6331189B1 (en) | 1999-10-18 | 2001-12-18 | Medtronic, Inc. | Flexible medical stent |
DE19951477A1 (en) | 1999-10-26 | 2001-05-03 | Biotronik Mess & Therapieg | Stent |
US6679910B1 (en) * | 1999-11-12 | 2004-01-20 | Latin American Devices Llc | Intraluminal stent |
US6280466B1 (en) | 1999-12-03 | 2001-08-28 | Teramed Inc. | Endovascular graft system |
US6673107B1 (en) * | 1999-12-06 | 2004-01-06 | Advanced Cardiovascular Systems, Inc. | Bifurcated stent and method of making |
US6387120B2 (en) | 1999-12-09 | 2002-05-14 | Advanced Cardiovascular Systems, Inc. | Stent and catheter assembly and method for treating bifurcations |
US6942674B2 (en) | 2000-01-05 | 2005-09-13 | Integrated Vascular Systems, Inc. | Apparatus and methods for delivering a closure device |
US6355063B1 (en) | 2000-01-20 | 2002-03-12 | Impra, Inc. | Expanded PTFE drug delivery graft |
US6736838B1 (en) | 2000-03-22 | 2004-05-18 | Zuli Holdings Ltd. | Method and apparatus for covering a stent |
GB0009030D0 (en) | 2000-04-12 | 2000-05-31 | Angiomed Ag | Self-expanding metal stent and method of making it |
US6626902B1 (en) | 2000-04-12 | 2003-09-30 | University Of Virginia Patent Foundation | Multi-probe system |
JP3654627B2 (en) | 2000-04-20 | 2005-06-02 | 川澄化学工業株式会社 | Stent |
US6776796B2 (en) | 2000-05-12 | 2004-08-17 | Cordis Corportation | Antiinflammatory drug and delivery device |
US6764519B2 (en) | 2000-05-26 | 2004-07-20 | Scimed Life Systems, Inc. | Ureteral stent |
US20030139803A1 (en) | 2000-05-30 | 2003-07-24 | Jacques Sequin | Method of stenting a vessel with stent lumenal diameter increasing distally |
US6800089B1 (en) | 2000-05-31 | 2004-10-05 | Advanced Cardiovascular Systems, Inc. | Mechanical attachment method of cover materials on stents |
US6572646B1 (en) | 2000-06-02 | 2003-06-03 | Advanced Cardiovascular Systems, Inc. | Curved nitinol stent for extremely tortuous anatomy |
WO2001095876A1 (en) | 2000-06-09 | 2001-12-20 | Baylor College Of Medicine | The combination of antimicrobial agents and bacterial interference to coat medical devices |
US6723373B1 (en) | 2000-06-16 | 2004-04-20 | Cordis Corporation | Device and process for coating stents |
US6805704B1 (en) | 2000-06-26 | 2004-10-19 | C. R. Bard, Inc. | Intraluminal stents |
US6540775B1 (en) * | 2000-06-30 | 2003-04-01 | Cordis Corporation | Ultraflexible open cell stent |
US6709451B1 (en) * | 2000-07-14 | 2004-03-23 | Norman Noble, Inc. | Channeled vascular stent apparatus and method |
US6440162B1 (en) | 2000-07-26 | 2002-08-27 | Advanced Cardiovascular Systems, Inc. | Stent having increased scaffolding expandable bar arms |
US6808533B1 (en) | 2000-07-28 | 2004-10-26 | Atrium Medical Corporation | Covered stent and method of covering a stent |
US6613078B1 (en) | 2000-08-02 | 2003-09-02 | Hector Daniel Barone | Multi-component endoluminal graft assembly, use thereof and method of implanting |
NO312223B1 (en) | 2000-09-05 | 2002-04-15 | Leiv Eiriksson Nyfotek As | Coated expandable stent |
US6554841B1 (en) | 2000-09-22 | 2003-04-29 | Scimed Life Systems, Inc. | Striped sleeve for stent delivery |
US20020072792A1 (en) | 2000-09-22 | 2002-06-13 | Robert Burgermeister | Stent with optimal strength and radiopacity characteristics |
US6695833B1 (en) * | 2000-09-27 | 2004-02-24 | Nellix, Inc. | Vascular stent-graft apparatus and forming method |
US6805898B1 (en) | 2000-09-28 | 2004-10-19 | Advanced Cardiovascular Systems, Inc. | Surface features of an implantable medical device |
US6485508B1 (en) | 2000-10-13 | 2002-11-26 | Mcguinness Colm P. | Low profile stent |
US6764507B2 (en) | 2000-10-16 | 2004-07-20 | Conor Medsystems, Inc. | Expandable medical device with improved spatial distribution |
US6786918B1 (en) | 2000-10-17 | 2004-09-07 | Medtronic Vascular, Inc. | Stent delivery system |
US6663664B1 (en) | 2000-10-26 | 2003-12-16 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent with time variable radial force |
US6656211B1 (en) | 2000-10-26 | 2003-12-02 | Scimed Life Systems, Inc. | Stent delivery system with improved tracking |
US6758859B1 (en) | 2000-10-30 | 2004-07-06 | Kenny L. Dang | Increased drug-loading and reduced stress drug delivery device |
US6770086B1 (en) | 2000-11-02 | 2004-08-03 | Scimed Life Systems, Inc. | Stent covering formed of porous polytetraflouroethylene |
AU2002233936A1 (en) * | 2000-11-07 | 2002-05-21 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal stent, self-fupporting endoluminal graft and methods of making same |
US6843802B1 (en) * | 2000-11-16 | 2005-01-18 | Cordis Corporation | Delivery apparatus for a self expanding retractable stent |
US6664335B2 (en) | 2000-11-30 | 2003-12-16 | Cardiac Pacemakers, Inc. | Polyurethane elastomer article with “shape memory” and medical devices therefrom |
US6589214B2 (en) * | 2000-12-06 | 2003-07-08 | Rex Medical, L.P. | Vascular introducer sheath with retainer |
US6645242B1 (en) | 2000-12-11 | 2003-11-11 | Stephen F. Quinn | Bifurcated side-access intravascular stent graft |
US6565599B1 (en) | 2000-12-28 | 2003-05-20 | Advanced Cardiovascular Systems, Inc. | Hybrid stent |
US6569194B1 (en) | 2000-12-28 | 2003-05-27 | Advanced Cardiovascular Systems, Inc. | Thermoelastic and superelastic Ni-Ti-W alloy |
US6641607B1 (en) | 2000-12-29 | 2003-11-04 | Advanced Cardiovascular Systems, Inc. | Double tube stent |
US6899727B2 (en) | 2001-01-22 | 2005-05-31 | Gore Enterprise Holdings, Inc. | Deployment system for intraluminal devices |
US6752829B2 (en) | 2001-01-30 | 2004-06-22 | Scimed Life Systems, Inc. | Stent with channel(s) for containing and delivering a biologically active material and method for manufacturing the same |
US6540777B2 (en) | 2001-02-15 | 2003-04-01 | Scimed Life Systems, Inc. | Locking stent |
US6790227B2 (en) | 2001-03-01 | 2004-09-14 | Cordis Corporation | Flexible stent |
US6679911B2 (en) * | 2001-03-01 | 2004-01-20 | Cordis Corporation | Flexible stent |
US6955686B2 (en) | 2001-03-01 | 2005-10-18 | Cordis Corporation | Flexible stent |
US6673104B2 (en) * | 2001-03-15 | 2004-01-06 | Scimed Life Systems, Inc. | Magnetic stent |
US6673105B1 (en) * | 2001-04-02 | 2004-01-06 | Advanced Cardiovascular Systems, Inc. | Metal prosthesis coated with expandable ePTFE |
US6756007B2 (en) | 2001-04-04 | 2004-06-29 | Bard Peripheral Vascular, Inc. | Method for preparing an implantable prosthesis for loading into a delivery apparatus |
US6764505B1 (en) | 2001-04-12 | 2004-07-20 | Advanced Cardiovascular Systems, Inc. | Variable surface area stent |
US6660034B1 (en) | 2001-04-30 | 2003-12-09 | Advanced Cardiovascular Systems, Inc. | Stent for increasing blood flow to ischemic tissues and a method of using the same |
US6685745B2 (en) * | 2001-05-15 | 2004-02-03 | Scimed Life Systems, Inc. | Delivering an agent to a patient's body |
US6629994B2 (en) | 2001-06-11 | 2003-10-07 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US6749629B1 (en) | 2001-06-27 | 2004-06-15 | Advanced Cardiovascular Systems, Inc. | Stent pattern with figure-eights |
US6673154B1 (en) * | 2001-06-28 | 2004-01-06 | Advanced Cardiovascular Systems, Inc. | Stent mounting device to coat a stent |
US6641611B2 (en) | 2001-11-26 | 2003-11-04 | Swaminathan Jayaraman | Therapeutic coating for an intravascular implant |
US6908480B2 (en) * | 2001-08-29 | 2005-06-21 | Swaminathan Jayaraman | Structurally variable stents |
US6656351B2 (en) | 2001-08-31 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Embolic protection devices one way porous membrane |
US6805703B2 (en) | 2001-09-18 | 2004-10-19 | Scimed Life Systems, Inc. | Protective membrane for reconfiguring a workpiece |
US6753071B1 (en) | 2001-09-27 | 2004-06-22 | Advanced Cardiovascular Systems, Inc. | Rate-reducing membrane for release of an agent |
US6693522B2 (en) * | 2001-10-12 | 2004-02-17 | Lear Corporation | System and method for tire pressure monitoring including automatic tire location recognition |
ATE380001T1 (en) | 2001-10-22 | 2007-12-15 | Terumo Corp | STENT AND METHOD FOR THE PRODUCTION THEREOF |
US20030077310A1 (en) | 2001-10-22 | 2003-04-24 | Chandrashekhar Pathak | Stent coatings containing HMG-CoA reductase inhibitors |
US20030083734A1 (en) | 2001-10-25 | 2003-05-01 | Curative Ag | Stent |
US7014654B2 (en) | 2001-11-30 | 2006-03-21 | Scimed Life Systems, Inc. | Stent designed for the delivery of therapeutic substance or other agents |
US20030114919A1 (en) | 2001-12-10 | 2003-06-19 | Mcquiston Jesse | Polymeric stent with metallic rings |
US6752826B2 (en) | 2001-12-14 | 2004-06-22 | Thoratec Corporation | Layered stent-graft and methods of making the same |
US6805707B1 (en) | 2001-12-27 | 2004-10-19 | Advanced Cardiovascular Systems, Inc. | Stent with improved ring and link pattern |
US7163553B2 (en) | 2001-12-28 | 2007-01-16 | Advanced Cardiovascular Systems, Inc. | Intravascular stent and method of use |
US7029493B2 (en) | 2002-01-25 | 2006-04-18 | Cordis Corporation | Stent with enhanced crossability |
US6989024B2 (en) * | 2002-02-28 | 2006-01-24 | Counter Clockwise, Inc. | Guidewire loaded stent for delivery through a catheter |
US6911039B2 (en) | 2002-04-23 | 2005-06-28 | Medtronic Vascular, Inc. | Integrated mechanical handle with quick slide mechanism |
US6761731B2 (en) | 2002-06-28 | 2004-07-13 | Cordis Corporation | Balloon-stent interaction to help reduce foreshortening |
US6802859B1 (en) | 2002-07-12 | 2004-10-12 | Endovascular Technologies, Inc. | Endovascular stent-graft with flexible bifurcation |
US6805706B2 (en) | 2002-08-15 | 2004-10-19 | Gmp Cardiac Care, Inc. | Stent-graft with rails |
US6818063B1 (en) | 2002-09-24 | 2004-11-16 | Advanced Cardiovascular Systems, Inc. | Stent mandrel fixture and method for minimizing coating defects |
CA2499710A1 (en) | 2002-09-30 | 2004-04-15 | Board Of Regents The University Of Texas System | Stent delivery system and method of use |
US20040093056A1 (en) | 2002-10-26 | 2004-05-13 | Johnson Lianw M. | Medical appliance delivery apparatus and method of use |
US6984244B2 (en) * | 2003-03-27 | 2006-01-10 | Endovascular Technologies, Inc. | Delivery system for endoluminal implant |
-
2002
- 2002-10-26 US US10/281,429 patent/US20040093056A1/en not_active Abandoned
-
2003
- 2003-10-25 AU AU2003301732A patent/AU2003301732B2/en not_active Ceased
- 2003-10-25 CA CA002503563A patent/CA2503563A1/en not_active Abandoned
- 2003-10-25 WO PCT/US2003/033967 patent/WO2004039242A2/en active IP Right Grant
- 2003-10-25 EP EP03809965A patent/EP1553903A4/en not_active Withdrawn
- 2003-10-25 JP JP2004548493A patent/JP4570957B2/en not_active Expired - Lifetime
-
2006
- 2006-02-17 US US11/357,366 patent/US7608099B2/en not_active Expired - Lifetime
-
2009
- 2009-09-17 US US12/561,657 patent/US8267987B2/en not_active Expired - Lifetime
Patent Citations (87)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3196876A (en) * | 1961-05-10 | 1965-07-27 | Maurice M Miller | Dilator |
US4606330A (en) * | 1983-08-09 | 1986-08-19 | Richard Wolf Gmbh | Device for disintegrating stones in bodily cavities or ducts |
US4893623A (en) * | 1986-12-09 | 1990-01-16 | Advanced Surgical Intervention, Inc. | Method and apparatus for treating hypertrophy of the prostate gland |
US5249585A (en) * | 1988-07-28 | 1993-10-05 | Bsd Medical Corporation | Urethral inserted applicator for prostate hyperthermia |
US5019085A (en) * | 1988-10-25 | 1991-05-28 | Cordis Corporation | Apparatus and method for placement of a stent within a subject vessel |
US5302906A (en) * | 1990-03-21 | 1994-04-12 | Siemens Aktiengesellschaft | Method and arrangement for determining a load angle of a generator which is connected to an electrical supply network |
US5159920A (en) * | 1990-06-18 | 1992-11-03 | Mentor Corporation | Scope and stent system |
US5433723A (en) * | 1991-10-11 | 1995-07-18 | Angiomed Ag | Apparatus for widening a stenosis |
US5817102A (en) * | 1992-05-08 | 1998-10-06 | Schneider (Usa) Inc. | Apparatus for delivering and deploying a stent |
US5409453A (en) * | 1992-08-12 | 1995-04-25 | Vidamed, Inc. | Steerable medical probe with stylets |
US5549644A (en) * | 1992-08-12 | 1996-08-27 | Vidamed, Inc. | Transurethral needle ablation device with cystoscope and method for treatment of the prostate |
US5690644A (en) * | 1992-12-30 | 1997-11-25 | Schneider (Usa) Inc. | Apparatus for deploying body implantable stent |
US6755855B2 (en) * | 1992-12-30 | 2004-06-29 | Boston Scientific Scimed, Inc. | Apparatus for deploying body implantable stents |
US6380457B1 (en) * | 1992-12-30 | 2002-04-30 | Boston Scientific Scimed, Inc. | Apparatus for deploying body implantable stents |
US5902333A (en) * | 1993-04-13 | 1999-05-11 | Boston Scientific Corporation | Prosthesis delivery system with dilating tip |
US5984964A (en) * | 1993-04-13 | 1999-11-16 | Boston Scientific Corporation | Prothesis delivery system |
US5603698A (en) * | 1993-04-13 | 1997-02-18 | Boston Scientific Corporation | Prosthesis delivery system |
US5824058A (en) * | 1993-05-20 | 1998-10-20 | Boston Scientific Corporation | Prosthesis delivery |
US5565211A (en) * | 1993-06-22 | 1996-10-15 | Crina S.A. | Composition for improving the digestibility of feed intended for ruminants |
US5320617A (en) * | 1993-06-25 | 1994-06-14 | Leach Gary E | Method of laser-assisted prostatectomy and apparatus for carrying out the method |
US5588949A (en) * | 1993-10-08 | 1996-12-31 | Heartport, Inc. | Stereoscopic percutaneous visualization system |
US5667522A (en) * | 1994-03-03 | 1997-09-16 | Medinol Ltd. | Urological stent and deployment device therefor |
US5746692A (en) * | 1994-05-05 | 1998-05-05 | Imagen Medical, Inc. | Catheter and endoscope system with distal protruding ball tip and method |
US5514093A (en) * | 1994-05-19 | 1996-05-07 | Scimed Life Systems, Inc. | Variable length balloon dilatation catheter |
US5601591A (en) * | 1994-09-23 | 1997-02-11 | Vidamed, Inc. | Stent for use in prostatic urethra, apparatus and placement device for same and method |
US5782838A (en) * | 1994-10-20 | 1998-07-21 | Medtronic Instent, Inc. | Cytoscope delivery system |
US6369355B1 (en) * | 1994-11-28 | 2002-04-09 | Advance Cardiovascular Systems, Inc. | Method and apparatus for direct laser cutting of metal stents |
US6325790B1 (en) * | 1995-04-11 | 2001-12-04 | Cordis Corporation | Soft tip catheter |
US5833694A (en) * | 1995-05-25 | 1998-11-10 | Medtronic, Inc. | Stent assembly and method of use |
US6656214B1 (en) * | 1995-09-08 | 2003-12-02 | Medtronic Ave, Inc. | Methods and apparatus for conformably sealing prostheses within body lumens |
US5803080A (en) * | 1995-12-20 | 1998-09-08 | Willy Rusch Ag | Instrument for interventional flexible tracheoscopy/bronchoscopy |
US6451025B1 (en) * | 1996-04-01 | 2002-09-17 | General Surgical Innovations, Inc. | Prosthesis and method for deployment within a body lumen |
US6802849B2 (en) * | 1996-08-23 | 2004-10-12 | Scimed Life Systems, Inc. | Stent delivery system |
US6663660B2 (en) * | 1996-08-23 | 2003-12-16 | Scimed Life Systems, Inc. | Stent delivery system having stent securement apparatus |
US5968052A (en) * | 1996-11-27 | 1999-10-19 | Scimed Life Systems Inc. | Pull back stent delivery system with pistol grip retraction handle |
US6669720B1 (en) * | 1997-01-28 | 2003-12-30 | George E. Pierce | Prosthesis for endovascular repair of abdominal aortic aneurysms |
US6086528A (en) * | 1997-09-11 | 2000-07-11 | Adair; Edwin L. | Surgical devices with removable imaging capability and methods of employing same |
US6019778A (en) * | 1998-03-13 | 2000-02-01 | Cordis Corporation | Delivery apparatus for a self-expanding stent |
US6669716B1 (en) * | 1998-03-31 | 2003-12-30 | Salviac Limited | Delivery catheter |
US6752819B1 (en) * | 1998-04-02 | 2004-06-22 | Salviac Limited | Delivery catheter |
US6780199B2 (en) * | 1998-05-15 | 2004-08-24 | Advanced Cardiovascular Systems, Inc. | Enhanced stent delivery system |
US6517569B2 (en) * | 1998-09-14 | 2003-02-11 | Endocare, Inc. | Insertion device for stents and methods for use |
US6162231A (en) * | 1998-09-14 | 2000-12-19 | Endocare, Inc. | Stent insertion device |
US6800081B2 (en) * | 1998-09-18 | 2004-10-05 | Aptus Endosystems, Inc. | Systems and methods for applying a suture within a blood vesel lumen |
US6203550B1 (en) * | 1998-09-30 | 2001-03-20 | Medtronic, Inc. | Disposable delivery device for endoluminal prostheses |
US20030144671A1 (en) * | 1998-09-30 | 2003-07-31 | Brooks Christopher J. | Delivery mechanism for implantable stents-grafts |
US6726712B1 (en) * | 1999-05-14 | 2004-04-27 | Boston Scientific Scimed | Prosthesis deployment device with translucent distal end |
US6375676B1 (en) * | 1999-05-17 | 2002-04-23 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent with enhanced delivery precision and stent delivery system |
US6695862B2 (en) * | 1999-05-17 | 2004-02-24 | Advanced Cardiovascular Systems, Inc. | Self-expanding stent with enhanced delivery precision and stent delivery system |
US6695812B2 (en) * | 1999-06-30 | 2004-02-24 | Advanced Cardiovascular Systems, Inc. | Catheter with enhanced flexibility |
US6689157B2 (en) * | 1999-07-07 | 2004-02-10 | Endologix, Inc. | Dual wire placement catheter |
US6695809B1 (en) * | 1999-09-13 | 2004-02-24 | Advanced Cardiovascular Systems, Inc. | Catheter balloon with a discontinuous elastomeric outer layer |
US6669718B2 (en) * | 1999-11-18 | 2003-12-30 | Petrus Besselink | Apparatus and method for placing bifurcated stents |
US6702849B1 (en) * | 1999-12-13 | 2004-03-09 | Advanced Cardiovascular Systems, Inc. | Method of processing open-celled microcellular polymeric foams with controlled porosity for use as vascular grafts and stent covers |
US6322586B1 (en) * | 2000-01-10 | 2001-11-27 | Scimed Life Systems, Inc. | Catheter tip designs and method of manufacture |
US6723113B1 (en) * | 2000-01-19 | 2004-04-20 | Cordis Neurovascular, Inc. | Inflatable balloon catheter seal and method |
US6808529B2 (en) * | 2000-02-11 | 2004-10-26 | Edwards Lifesciences Corporation | Apparatus and methods for delivery of intraluminal prostheses |
US6699277B1 (en) * | 2000-03-09 | 2004-03-02 | Diseno Y Desarrollo Medica, S.A. De C.V. | Stent with cover connectors |
US6773446B1 (en) * | 2000-08-02 | 2004-08-10 | Cordis Corporation | Delivery apparatus for a self-expanding stent |
US6743219B1 (en) * | 2000-08-02 | 2004-06-01 | Cordis Corporation | Delivery apparatus for a self-expanding stent |
US6736828B1 (en) * | 2000-09-29 | 2004-05-18 | Scimed Life Systems, Inc. | Method for performing endoluminal fundoplication and apparatus for use in the method |
US6761708B1 (en) * | 2000-10-31 | 2004-07-13 | Advanced Cardiovascular Systems, Inc. | Radiopaque marker for a catheter and method of making |
US6623491B2 (en) * | 2001-01-18 | 2003-09-23 | Ev3 Peripheral, Inc. | Stent delivery system with spacer member |
US6749627B2 (en) * | 2001-01-18 | 2004-06-15 | Ev3 Peripheral, Inc. | Grip for stent delivery system |
US6699274B2 (en) * | 2001-01-22 | 2004-03-02 | Scimed Life Systems, Inc. | Stent delivery system and method of manufacturing same |
US6802846B2 (en) * | 2001-02-12 | 2004-10-12 | Ams Research Corporation | Foreign body retrieval device and method |
US6723071B2 (en) * | 2001-03-14 | 2004-04-20 | Scimed Life Systems, Inc. | Rapid exchange stent delivery system and associated components |
US6761733B2 (en) * | 2001-04-11 | 2004-07-13 | Trivascular, Inc. | Delivery system and method for bifurcated endovascular graft |
US6733521B2 (en) * | 2001-04-11 | 2004-05-11 | Trivascular, Inc. | Delivery system and method for endovascular graft |
US6676692B2 (en) * | 2001-04-27 | 2004-01-13 | Intek Technology L.L.C. | Apparatus for delivering, repositioning and/or retrieving self-expanding stents |
US20020161425A1 (en) * | 2001-04-30 | 2002-10-31 | Scimed Life Systems, Inc. | Endoscopic stent delivery system and method |
US20020183763A1 (en) * | 2001-05-17 | 2002-12-05 | Callol Joseph R. | Stent and catheter assembly and method for treating bifurcations |
US6790220B2 (en) * | 2001-06-08 | 2004-09-14 | Morris Innovative Research, Inc. | Method and apparatus for sealing access |
US6676693B1 (en) * | 2001-06-27 | 2004-01-13 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for delivering a self-expanding stent |
US6761703B2 (en) * | 2001-07-03 | 2004-07-13 | Scimed Life Systems, Inc. | Catheter incorporating a high column high column strength distal tip region |
US6569085B2 (en) * | 2001-08-16 | 2003-05-27 | Syntheon, Llc | Methods and apparatus for delivering a medical instrument over an endoscope while the endoscope is in a body lumen |
US6790223B2 (en) * | 2001-09-21 | 2004-09-14 | Scimed Life Systems, Inc. | Delivering a uretheral stent |
US6752825B2 (en) * | 2001-10-02 | 2004-06-22 | Scimed Life Systems, Inc | Nested stent apparatus |
US20030074045A1 (en) * | 2001-10-12 | 2003-04-17 | Jon Buzzard | Locking handle deployment mechanism for medical device and method |
US6746423B1 (en) * | 2001-11-01 | 2004-06-08 | Advanced Cardiovascular Systems, Inc. | Catheter having improved rapid exchange junction |
US6663880B1 (en) * | 2001-11-30 | 2003-12-16 | Advanced Cardiovascular Systems, Inc. | Permeabilizing reagents to increase drug delivery and a method of local delivery |
US6773448B2 (en) * | 2002-03-08 | 2004-08-10 | Ev3 Inc. | Distal protection devices having controllable wire motion |
US6780182B2 (en) * | 2002-05-23 | 2004-08-24 | Adiana, Inc. | Catheter placement detection system and operator interface |
US6773447B2 (en) * | 2002-07-02 | 2004-08-10 | Sentient Engineering & Technology, Llc | Balloon catheter and treatment apparatus |
US20040006380A1 (en) * | 2002-07-05 | 2004-01-08 | Buck Jerrick C. | Stent delivery system |
US6702850B1 (en) * | 2002-09-30 | 2004-03-09 | Mediplex Corporation Korea | Multi-coated drug-eluting stent for antithrombosis and antirestenosis |
US6673101B1 (en) * | 2002-10-09 | 2004-01-06 | Endovascular Technologies, Inc. | Apparatus and method for deploying self-expanding stents |
Cited By (62)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9925074B2 (en) | 1999-02-01 | 2018-03-27 | Board Of Regents, The University Of Texas System | Plain woven stents |
US8974516B2 (en) | 1999-02-01 | 2015-03-10 | Board Of Regents, The University Of Texas System | Plain woven stents |
US8876880B2 (en) | 1999-02-01 | 2014-11-04 | Board Of Regents, The University Of Texas System | Plain woven stents |
US8414635B2 (en) | 1999-02-01 | 2013-04-09 | Idev Technologies, Inc. | Plain woven stents |
US8267987B2 (en) | 2002-10-26 | 2012-09-18 | Merit Medical Systems, Inc. | Medical appliance delivery apparatus and method of use |
US20040193243A1 (en) * | 2003-03-31 | 2004-09-30 | Mangiardi Eric K. | Medical appliance optical delivery and deployment apparatus and method |
US8298277B2 (en) | 2003-03-31 | 2012-10-30 | Merit Medical Systems, Inc. | Medical appliance optical delivery and deployment apparatus and method |
US20110082426A1 (en) * | 2003-06-16 | 2011-04-07 | Ethicon Endo-Surgery, Inc. | Subcutaneous self attaching injection port with integral moveable retention members |
US8007474B2 (en) | 2003-06-16 | 2011-08-30 | Ethicon Endo-Surgery, Inc. | Implantable medical device with reversible attachment mechanism and method |
US8758303B2 (en) | 2003-06-16 | 2014-06-24 | Ethicon Endo-Surgery, Inc. | Injection port with applier |
US8715243B2 (en) | 2003-06-16 | 2014-05-06 | Ethicon Endo-Surgery, Inc. | Injection port applier with downward force actuation |
US20100130941A1 (en) * | 2003-06-16 | 2010-05-27 | Conlon Sean P | Audible And Tactile Feedback |
US8864717B2 (en) | 2003-06-16 | 2014-10-21 | Ethicon Endo-Surgery, Inc. | Subcutaneous self attaching injection port with integral moveable retention members |
US20100211085A1 (en) * | 2003-06-16 | 2010-08-19 | Ethicon Endo-Surgery, Inc. | Injection Port with Extendable and Retractable Fasteners |
US20100217199A1 (en) * | 2003-06-16 | 2010-08-26 | Ethicon Endo-Surgery, Inc. | Method of Repositioning an Injection Port |
US20100234808A1 (en) * | 2003-06-16 | 2010-09-16 | Uth Joshua R | Injection Port Applier with Downward Force Actuation |
US8764713B2 (en) | 2003-06-16 | 2014-07-01 | Ethicon Endo-Surgery, Inc. | Method of repositioning an injection port |
US8211127B2 (en) | 2003-06-16 | 2012-07-03 | Ethicon Endo-Surgery, Inc. | Injection port with extendable and retractable fasteners |
US7967829B2 (en) | 2003-10-09 | 2011-06-28 | Boston Scientific Scimed, Inc. | Medical device delivery system |
US20050080476A1 (en) * | 2003-10-09 | 2005-04-14 | Gunderson Richard C. | Medical device delivery system |
US20070149947A1 (en) * | 2003-12-19 | 2007-06-28 | Byrum Randal T | Audible and tactile feedback |
US7850660B2 (en) | 2003-12-19 | 2010-12-14 | Ethicon Endo-Surgery, Inc. | Implantable medical device with simultaneous attachment mechanism and method |
US20060293625A1 (en) * | 2003-12-19 | 2006-12-28 | Hunt John V | Implantable medical device with cover and method |
US8162897B2 (en) | 2003-12-19 | 2012-04-24 | Ethicon Endo-Surgery, Inc. | Audible and tactile feedback |
US8702744B2 (en) * | 2005-05-09 | 2014-04-22 | Nexeon Medsystems, Inc. | Apparatus and methods for renal stenting |
US20060253186A1 (en) * | 2005-05-09 | 2006-11-09 | Paragon Intellectual Properties, Llc | Apparatus and methods for renal stenting |
US7731654B2 (en) | 2005-05-13 | 2010-06-08 | Merit Medical Systems, Inc. | Delivery device with viewing window and associated method |
US7918844B2 (en) | 2005-06-24 | 2011-04-05 | Ethicon Endo-Surgery, Inc. | Applier for implantable medical device |
AU2006202530B2 (en) * | 2005-06-24 | 2012-04-12 | Ethicon Endo-Surgery, Inc. | Implantable medical device with indicator |
US20070010790A1 (en) * | 2005-06-24 | 2007-01-11 | Byrum Randal T | Injection port |
US7651483B2 (en) | 2005-06-24 | 2010-01-26 | Ethicon Endo-Surgery, Inc. | Injection port |
US7561916B2 (en) * | 2005-06-24 | 2009-07-14 | Ethicon Endo-Surgery, Inc. | Implantable medical device with indicator |
US20070100279A1 (en) * | 2005-11-03 | 2007-05-03 | Paragon Intellectual Properties, Llc | Radiopaque-balloon microcatheter and methods of manufacture |
US20080051867A1 (en) * | 2006-08-28 | 2008-02-28 | Davila Luis A | Multiple in vivo implant delivery device |
US9408729B2 (en) | 2006-10-22 | 2016-08-09 | Idev Technologies, Inc. | Secured strand end devices |
US9149374B2 (en) | 2006-10-22 | 2015-10-06 | Idev Technologies, Inc. | Methods for manufacturing secured strand end devices |
US8739382B2 (en) | 2006-10-22 | 2014-06-03 | Idev Technologies, Inc. | Secured strand end devices |
US8876881B2 (en) | 2006-10-22 | 2014-11-04 | Idev Technologies, Inc. | Devices for stent advancement |
US8966733B2 (en) | 2006-10-22 | 2015-03-03 | Idev Technologies, Inc. | Secured strand end devices |
US9895242B2 (en) | 2006-10-22 | 2018-02-20 | Idev Technologies, Inc. | Secured strand end devices |
US9629736B2 (en) | 2006-10-22 | 2017-04-25 | Idev Technologies, Inc. | Secured strand end devices |
US10470902B2 (en) | 2006-10-22 | 2019-11-12 | Idev Technologies, Inc. | Secured strand end devices |
US9408730B2 (en) | 2006-10-22 | 2016-08-09 | Idev Technologies, Inc. | Secured strand end devices |
US8419788B2 (en) | 2006-10-22 | 2013-04-16 | Idev Technologies, Inc. | Secured strand end devices |
US9585776B2 (en) | 2006-10-22 | 2017-03-07 | Idev Technologies, Inc. | Secured strand end devices |
US20150025614A1 (en) * | 2008-02-07 | 2015-01-22 | Intuitive Surgical Operations, Inc. | Stent Delivery Under Direct Visualization |
US10278849B2 (en) * | 2008-02-07 | 2019-05-07 | Intuitive Surgical Operations, Inc. | Stent delivery under direct visualization |
US11241325B2 (en) | 2008-02-07 | 2022-02-08 | Intuitive Surgical Operations, Inc. | Stent delivery under direct visualization |
US11376399B2 (en) | 2008-10-10 | 2022-07-05 | Biosensors International Group, Ltd. | Inventory sparing catheter system |
US20100094257A1 (en) * | 2008-10-10 | 2010-04-15 | Stalker Kent C B | Inventory sparing catheter system |
US20110230899A1 (en) * | 2009-10-23 | 2011-09-22 | Medi-Globe Vascutec Gmbh | Surgical device for feeding at least one suture thread through the edge area of a tissue opening of an individual and method for operating such a device |
US9023095B2 (en) | 2010-05-27 | 2015-05-05 | Idev Technologies, Inc. | Stent delivery system with pusher assembly |
US10987239B2 (en) | 2018-05-30 | 2021-04-27 | Vesper Medical, Inc. | Rotary handle stent delivery system and method |
US11234848B2 (en) | 2018-05-30 | 2022-02-01 | Vesper Medical, Inc. | Rotary handle stent delivery system and method |
US10441449B1 (en) | 2018-05-30 | 2019-10-15 | Vesper Medical, Inc. | Rotary handle stent delivery system and method |
US10449073B1 (en) | 2018-09-18 | 2019-10-22 | Vesper Medical, Inc. | Rotary handle stent delivery system and method |
US10736762B2 (en) | 2018-09-18 | 2020-08-11 | Vesper Medical, Inc. | Rotary handle stent delivery system and method |
US10993825B2 (en) | 2018-09-18 | 2021-05-04 | Vesper Medical, Inc. | Rotary handle stent delivery system and method |
US11160676B2 (en) | 2018-09-18 | 2021-11-02 | Vesper Medical, Inc. | Rotary handle stent delivery system and method |
US11419744B2 (en) | 2018-09-18 | 2022-08-23 | Vesper Medical, Inc. | Rotary sheath withdrawal system and method |
US11219541B2 (en) | 2020-05-21 | 2022-01-11 | Vesper Medical, Inc. | Wheel lock for thumbwheel actuated device |
US11491037B2 (en) | 2020-05-21 | 2022-11-08 | Vesper Medical, Inc. | Wheel lock for thumbwheel actuated device |
Also Published As
Publication number | Publication date |
---|---|
US7608099B2 (en) | 2009-10-27 |
EP1553903A2 (en) | 2005-07-20 |
JP2006503671A (en) | 2006-02-02 |
AU2003301732B2 (en) | 2007-06-14 |
CA2503563A1 (en) | 2004-05-13 |
US8267987B2 (en) | 2012-09-18 |
US20100004732A1 (en) | 2010-01-07 |
WO2004039242A2 (en) | 2004-05-13 |
WO2004039242A3 (en) | 2004-08-12 |
JP4570957B2 (en) | 2010-10-27 |
AU2003301732A1 (en) | 2004-05-25 |
EP1553903A4 (en) | 2008-03-19 |
US20060200222A1 (en) | 2006-09-07 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7608099B2 (en) | Medical appliance delivery apparatus and method of use | |
US8298277B2 (en) | Medical appliance optical delivery and deployment apparatus and method | |
EP1740252B1 (en) | Distal wire stop | |
US8292872B2 (en) | Distal wire stop having adjustable handle | |
EP1653884B1 (en) | System for introducing a prosthesis | |
US7604660B2 (en) | Bifurcated medical appliance delivery apparatus and method | |
US8876854B2 (en) | Implant release mechanism | |
US20070179587A1 (en) | Apparatus and methods for deployment of custom-length prostheses | |
US20120136425A1 (en) | Slotted pusher rod for flexible delivery system | |
JP2007533400A (en) | System and method for introducing multiple medical devices |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: ALVEOLUS, NORTH CAROLINA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:JOHNSON, LIANN M.;SHERBURNE, PAUL S.;HECK, ALICIA;AND OTHERS;REEL/FRAME:013689/0460;SIGNING DATES FROM 20021209 TO 20030109 |
|
AS | Assignment |
Owner name: ALVEOLUS, INC., NORTH CAROLINA Free format text: CORRECTIVE ASSIGNMENT TO CORRECT THE ASSIGNEE'S NAME PREVIOUSLY RECORDED ON REEL 013689, FRAME 0640;ASSIGNORS:JOHNSON, LIANN M.;SHERBURNE, PAUL S.;HECK, ALICIA;AND OTHERS;REEL/FRAME:016248/0272;SIGNING DATES FROM 20021209 TO 20030109 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO PAY ISSUE FEE |