US20020177904A1 - Removable stent for body lumens - Google Patents
Removable stent for body lumens Download PDFInfo
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- US20020177904A1 US20020177904A1 US10/196,845 US19684502A US2002177904A1 US 20020177904 A1 US20020177904 A1 US 20020177904A1 US 19684502 A US19684502 A US 19684502A US 2002177904 A1 US2002177904 A1 US 2002177904A1
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- Prior art keywords
- stent
- coating
- filament
- polymer
- suture
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/88—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure the wire-like elements formed as helical or spiral coils
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/08—Materials for coatings
- A61L31/10—Macromolecular materials
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2/07—Stent-grafts
- A61F2002/072—Encapsulated stents, e.g. wire or whole stent embedded in lining
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2210/0004—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof bioabsorbable
Definitions
- the field of art to which this invention relates is medical devices, in particular, removable stent devices having bioabsorbable or biodegradable polymer coatings.
- stent medical devices or other types of endoluminal mechanical support devices, to keep a duct, vessel or other body lumen open in the human body has developed into a primary therapy for lumen stenosis or obstruction.
- the use of stents in various surgical procedures has quickly become accepted as experience with stent devices accumulates, and the number of surgical procedures employing them increases as their advantages become more widely recognized.
- a permanent stent is designed to be maintained in a body lumen for an indeterminate amount of time.
- Temporary stents are designed to be maintained in a body lumen for a limited period of time in order to maintain the patency of the body lumen, for example, after trauma to a lumen caused by a surgical procedure or an injury.
- Permanent stents are typically designed to provide long term support for damaged or traumatized wall tissues of the lumen.
- There are numerous conventional applications for permanent stents including cardiovascular, urological, gastrointestinal, and gynecological applications.
- Temporary stents may advantageously be eliminated from body lumens after a predetermined, clinically appropriate period of time, for example, after the traumatized tissues of the lumen have healed and a stent is no longer needed to maintain the patency of the lumen.
- temporary stents can be used as substitutes for in-dwelling catheters for applications in the treatment of prostatic obstruction or other urethral stricture diseases.
- Another indication for temporary stents in a body lumen is after energy ablation, such as laser or thermal ablation, or irradiation of prostatic tissue, in order to control post-operative acute urinary retention or other body fluid retention.
- metal stents may become encrusted, encapsulated, epithelialized or ingrown with body tissue.
- the stents are known to migrate on occasion from their initial insertion location.
- Such stents are known to cause irritation to the surrounding tissues in a lumen.
- metals are typically much harder and stiffer than the surrounding tissues in a lumen, this may result in an anatomical or physiological mismatch, thereby damaging tissue or eliciting unwanted biologic responses.
- permanent metal stents are designed to be implanted for an indefinite period of time, it is sometimes necessary to remove permanent metal stents. For example, if there is a biological response requiring surgical intervention, often the stent must be removed through a secondary procedure. If the metal stent is a temporary stent, it will also have to be removed after a clinically appropriate period of time. Regardless of whether the metal stent is categorized as permanent or temporary, if the stent has been encapsulated, epithelialized, etc., the surgical removal of the stent will resultingly cause undesirable pain and discomfort to the patient and possibly additional trauma to the lumen tissue. In addition to the pain and discomfort, the patient must be subjected to an additional time consuming and complicated surgical procedure with the attendant risks of surgery, in order to remove the metal stent.
- bioabsorbable and biodegradable materials for manufacturing temporary stents.
- the conventional bioabsorbable or bioresorbable materials from which such stents are made are selected to absorb or degrade over time, thereby eliminating the need for subsequent surgical procedures to remove the stent from the body lumen.
- bioabsorbable and biodegradable materials tend to have excellent biocompatibility characteristics, especially in comparison to most conventionally used biocompatible metals in certain sensitive patients.
- stents made from bioabsorbable and biodegradable materials are made from bioabsorbable and biodegradable materials.
- the mechanical properties can be designed to substantially eliminate or reduce the stiffness and hardness that is often associated with metal stents, which can contribute to the propensity of a stent to damage a vessel or lumen.
- the temporary stent readily passes out of the body, or is removed as, a limp, flexible string-like member, and irritation, obstruction, pain or discomfort to the patient is either eliminated, or if present, is minimal.
- a stent for insertion into a body lumen which is manufactured from a flexible filament member, such as a suture, and then coated with a biodegradable or bioabsorbale polymer such that the member is formed into a relatively rigid stent, and when in the body, softens back into a flexible filament member which is easily passed or removed from the body lumen after a specific therapeutic period of time.
- an implantable stent for use in body lumens, wherein such lumens exist as part of the natural anatomy or are made surgically.
- the stent is an elongate, hollow member having a helical or coiled structure, and in a preferred embodiment has a helical structure having a plurality of coils.
- the structure has a longitudinal axis and a longitudinal passage.
- the coils have a pitch.
- the structure is made from a flexible, limp filament or fiber, such as a surgical suture, having an exterior polymeric coating.
- the polymeric coating is a bioabsorbable or biodegradable polymer, or blend thereof.
- the coating is solid, and of sufficient thickness to effectively cause the flexible, limp member to be maintained in a substantially rigid, fixed state as a structure.
- the rate of degradation or absorption of the coating in vivo is sufficient to effectively soften or be removed from the outer surface of the filament within the desired therapeutic period. This effectively provides that as the coating degrades, softens or is absorbed in vivo, it loses its mechanical integrity. This allows the filament to revert to its natural, flexible limp state, causing the stent structure to effectively collapse, and the filament may be removed or eliminated from the lumen.
- the progressively degrading and/or absorbing coating causes the stent to soften and collapse into a flexible filament that can readily pass out of the body lumen, either by manipulation or through natural expulsion with body fluids, thereby minimizing the possibility of causing obstruction, pain or discomfort.
- Yet another aspect of the present invention is the above-described stent made from a fiber which is radio-opaque.
- a stent of the present invention is provided.
- the stent is an elongate, hollow member and in a preferred embodiment has a helical structure having a plurality of coils.
- the member has a longitudinal axis.
- the coils have a pitch.
- the structure is made from a flexible, limp filament or a fiber, having an outer surface and an exterior polymeric coating.
- the stent is inserted into a body lumen. The exposure to in vivo body fluids causes the exterior coating to absorb and/or degrade and soften, thereby causing the stent structure to collapse and return to a limp, flexible filament that can then be either eliminated by the passage of body fluids or manually removed.
- FIG. 1 is a perspective view of a preferred embodiment of a stent device of the present invention mounted to the distal end of an applicator instrument.
- FIG. 2 is a perspective view of the stent and applicator of FIG. 1, prior to loading the stent onto the applicator instrument.
- FIG. 3 is a side view of a stent device of the present invention, having a helical configuration.
- FIG. 4 is a cross-sectional view of the fiber used to make the stent of FIG. 3 taken along View Line 4 - 4 illustrating a circular cross-section.
- FIG. 5 is a side view of the stent and applicator device of FIG. 1, where the device is shown in the ready position, prior to application.
- FIG. 6 is a side view of the stent and applicator device of FIG. 5, illustrating the position of the stent relative to the applicator when the stent is partially deployed by engaging the applicator trigger.
- FIG. 7 illustrates the relative positions of the stent to the applicator of FIG. 6 when the stent is fully deployed by fully engaging the applicator trigger.
- FIG. 8 illustrates the stent of the present invention fully deployed in the urethra and prostate of a patient, providing for a patent lumen.
- FIG. 9 illustrates a stent of the present invention emplaced in the urethra of a patient after the coating has degraded, been absorbed or otherwise broken down or softened; showing the stent being removed from the body as an elongated, soft, flexible filament.
- FIG. 10 is a schematic of a mandrel used to manufacture stents in Example 3.
- the stent 10 is seen to be a helical structure having a series of connected coils 20 .
- the coils are made from filament 100 .
- the term filament as used herein is defined to include not only filaments but fibers as well, and is used interchangeably with the term fiber. It is preferred that filament 100 be a continuous filament, however, it is possible to make stent 10 from two or more sections of filament which are subsequently connected or hinged together.
- the filament 100 is seen to have inner flexible member 110 and outer coating 130 .
- the inner flexible member 110 is seen to have outer surface 115 .
- Outer coating 130 is seen to have inner surface 135 and exterior surface 140 .
- inner surface 135 is in contact with, and affixed to, the outer surface 115 .
- the stent is seen to have a longitudinal axis 70 , and internal passageway 11 .
- the stent 10 is seen to have a first distal section 30 of coils 20 connected to a second section 50 of coils 20 , wherein the sections 30 and 50 are connected by hinged connecting fiber 60 .
- the distal section 30 of coils adjacent to hinged connecting fiber 60 forms an anchoring section which is inserted distal to the external sphincter.
- the proximal section 50 of the stent 10 is maintained within the prostatic urethra.
- Proximal section 50 is seen to have coils 20 having diameter 24 , and also has passageway 51 .
- the distal section 30 of stent 10 has coils 20 having a diameter 22 .
- Distal section 30 also has a passageway 31 .
- Passage ways 31 and 51 are in communication to form passageway 11 of stent 10 .
- one preferred embodiment of the stent 10 of the present invention has a filament 100 having a circular cross-sectional configuration.
- the filament 100 may have various configurations depending upon the application including round, square, polygonal, curved, oval, and combinations thereof and equivalents thereof.
- the advantages of fiber of the present invention having a round cross-section include ease of the stent manufacturing process due to a possible on-line, one-step transition from the fiber to the stent in future manufacturing processes, flexibility during the stent deployment by being able to tailor the length of the stent during a surgical procedure to fit a particular patient's anatomy, and the use of commercially available filaments such as sutures.
- the stent 10 is preferably manufactured from a flexible, polymeric filament 100 having a desired cross-sectional configuration.
- the length and overall diameter of the stent 10 will depend upon a number of factors including the anatomy of the patient, the size of the anatomy and the type of surgical procedure which has effected the urethral lumen.
- the overall length of a stent 10 useful in the practice of the present invention will be sufficient to effectively maintain the lumen passage open.
- the length for urethral applications in and adult male the length will be about 10 mm to about 200 mm, more typically about 20 mm to about 100 mm, and preferably about 40 mm to about 80 mm.
- the diameter of a stent 10 of the present invention will be sufficient to effectively maintain patency of the lumen.
- the diameter in the prostatic urethra will typically be about 2 mm to about 25 mm, more typically about 4 mm to about 15 mm, and preferably about 6 mm to about 10 mm.
- the diameter of the section used to anchor distal to the external sphincter will be about 2 mm to about 25 mm, more typically about 4 mm to about 15 mm, and preferably about 6 mm to about 10 mm.
- the major cross-sectional dimension of a fiber used to manufacture a stent of the present invention will be sufficient to provide effective support and flexibility.
- the diameter for urethral applications will be about 0.1 mm to about 4 mm, more typically about 0.5 mm to about 3 mm, and preferably about 1 mm to about 2 mm.
- the pitch, length, diameter and fiber diameter of the stents of the present invention will be sufficient to effectively provide sufficient support in response to radial stress of the urethral vessel walls, while providing for ease of insertion and stability while inserted in the urethral lumen, as well as desired flexibility and lumen patency.
- the pitch of the stent is defined to be the number of coils per unit length. In this patent application specification, for this example, pitch is defined as the number of coils per centimeter of stent length.
- the pitch will be about 2.5 to about 100, more typically about 3 to about 20, and preferably about 5 to about 10.
- the stents of the present invention may have spaces between adjacent coils.
- the flexible members 110 coated with coatings 130 to form filaments 100 of the present invention will preferably be selected to have sufficient flexibility and softness and limpness to effectively provide for a stent that will collapse and be easily removed from a body lumen.
- the materials useful for the flexible member include flexible, limp monofilament and braided string-like members. It is particularly preferred to use conventional nonabsorbable sutures, such as monofilament or braided polypropylene, silk, polyester, nylon and the like and equivalents thereof.
- the flexible members may also be conventional absorbable sutures, monofilament or braided, including 95/5 lactide/glycolide, and polydioxanone, and the like.
- the flexible member 110 may also be made from yarn type materials made from biocompatible fibers that are “spun” together to form the yarn.
- the outer coatings useful for the stents and filaments of the present invention will be conventional biodegradable or bioabsorbable polymers, and blends thereof, including polymers made from monomers selected from the group consisting of lactide, glycolide, para-dioxanone, caprolactone, and trimethylene carbonate, caprolactone, blends thereof and copolymers thereof.
- the effect of the degradation or absorption of the polymeric coating is to convert the filament back into a soft, flexible member after a predetermined time period, such that the stent effectively collapses, and the flexible member can then be easily removed or passed from the lumen.
- the progressively degrading stent can readily pass through the body or be removed from the lumen without causing obstruction.
- the types of polymeric coatings that can advantageously provide stiffness to form a filament 100 include polymers with glass transition temperatures above room temperature and preferably above 55° C., and most preferably above about 120° C. These materials may be amorphous, that is, not display crystallinity. Polymers that have glass transition temperatures that are low, especially below room temperature, will generally require some crystallinity to provide the dimensional stability and stiffness to function in the present application. These can be described as semicrystalline.
- water soluble polymers for the coating there are two general classes of water soluble polymers: ionic and non-ionic.
- polyacrylamides In general of use are polyacrylamides, polyacrylic acid polymers, polyethers (especially the polyethylene glycols or polyethylene oxides), vinyl polymers such as some polyvinyl alcohols and some poly(N-vinyl pyrrolidone)s.
- Certain polysaccharide gums may also be useful; certain hydroxy celluloses, such as hydroxy methyl cellulose or certain hydroxy isopropyl cellulose are also useful.
- Polyamide nylon
- Polyamide may be used as a component to advantage because it can provide mechanical strength, absorbs some water, etc.
- a possible preferred blend component is polyethylene glycol (PEG or polyethylene oxide, PEO), especially those higher molecular weight resins that are semicrystalline.
- the melting point of PEG is about 60° C., which is high enough to meet requirements of a coating useful in the present invention.
- the PEO may be blended with nylon.
- biodegradable polymers made from poly glycolide/lactide copolymers, polycaprolactone, and the like may be used for the outer coating of the filament 100 .
- polyoxaesters can be utilized which are water soluble and degrade by hydrolysis. Other suitable polymers are found in U.S. Pat. No. 5,980,551, which is incorporated by reference.
- a stent must be designed to withstand radial stresses in order to perform its function of maintaining a passage through a lumen open.
- the mechanical capability of the stents of the present invention to withstand radial stresses when the stent is emplaced in the body lumen is provided primarily by the biodegradable/bioabsorbable material in the outer coating.
- the strength and stiffness and thickness of this material in the outer coating is sufficient to be effectively withstand the loads necessary to keep the stent functional.
- the coating can be designed to fulfill the mechanical requirements of keeping the body lumen patent or open for the specific therapeutic time period.
- the remaining filament After the coating has degraded/absorbed and effectively been removed from the stent structure by body fluids, the remaining filament returns to its soft, pliable, fibrillar state as a flexible member. The remaining soft filament is readily excreted or removed from the lumen.
- the coated filaments of the present invention may be made by conventional processes including co-extrusion, melt coating, solution coating or powder coating followed by spreading the coating by melting, etc., and the like.
- the inner flexible member can be a mono-filament extruded material or can be made from a multi-filament braid.
- the outer coating can be added on top of the flexible member either by melt coating or solution coating by passing the inner core through a bath, through coating rollers, brushes, spraying and/or a die.
- the polymers and blends that are used to form the coating can be used as a drug delivery matrix.
- the coating material would be mixed with a therapeutic agent.
- therapeutic agents which may be administered via the pharmaceutical compositions of the invention include, without limitation: anti-infectives such as antibiotics and anti-viral agents; analgesics and analgesic combinations; anti-inflammatory agents; hormones such as steroids; bone regenerating growth factors; and naturally derived or genetically engineered proteins, polysaccharides, glycoproteins, or lipoproteins.
- Matrix formulations may be formulated by mixing one or more therapeutic agents with the polymer.
- the therapeutic agent may be present as a liquid, a finely divided solid, or any other appropriate physical form.
- the matrix will include one or more additives, such as diluents, carriers, excipients, stabilizers or the like.
- the amount of therapeutic agent will depend on the particular drug being employed and medical condition being treated. Typically, the amount of drug represents about 0.001 percent to about 70 percent, more typically about 0.001 percent to about 50 percent, most typically about 0.001 percent to about 20 percent by weight of the matrix. The quantity and type of polymer incorporated into the drug delivery matrix will vary depending on the release profile desired and the amount of drug employed.
- the polymer coating Upon contact with body fluids, the polymer coating undergoes gradual degradation (mainly through hydrolysis) or absorption with concomitant release of the dispersed drug for a sustained or extended period. This can result in prolonged delivery (over, say 1 to 5,000 hours, preferably 2 to 800 hours) of effective amounts (say, 0.0001 mg/kg/hour to 10 mg/kg/hour) of the drug.
- This dosage form can be administered as is necessary depending on the subject being treated, the severity of the affliction, the judgment of the prescribing physician, and the like. Following this or similar procedures, those skilled in the art will be able to prepare a variety of formulations.
- the stents 10 of the present invention when made from the coated filament 100 may be manufactured in the following manner using a winding process.
- a filament 100 is wound about a mandrel by heating the filament 100 and then coiling it around the mandrel. The assembly of the mandrel and the coil are annealed under constraint and then the mandrel is removed. The pitch and diameter of the coils are selected to provide the desired size and shape of stent.
- the filament 100 may be wound about the mandrel without heat, for example immediately upon entering a coating bath or melt bath, or the uncoated flexible member 110 can be wound about a mandrel, and then the coating can be applied in a conventional manner, and cured as necessary.
- the stents of the present invention may be utilized in the following manner in urethral stent placement procedures as illustrated in FIGS. 1, 2, 5 , 6 , 7 and 8 .
- a stent 10 is placed upon the distal end of an applicator instrument 200 .
- Instrument 200 is seen to have handle 250 having grip 255 .
- the shaft retention member 290 At the top 257 of the handle 250 is mounted the shaft retention member 290 .
- Retention member 290 is seen to have longitudinal passageway 292 , front 295 and back 296 .
- the mounting tube 240 is seen to have distal end 242 and proximal end 244 .
- Mounting tube 240 is seen to have passage 248 .
- the proximal end 244 of tube 240 is seen to be mounted in passage way 292 such that the inner passageway 248 is in communication with passageway 292 .
- Slidably mounted in passageway 248 is the applicator tube 220 .
- Tube 220 has distal end 222 , proximal end 224 , and passageway 226 .
- Mounted to the proximal end 224 of tube 220 is the mounting block 300 , which is affixed to end 224 by pin 309 .
- Mounted to the bottom of block 300 is rack gear member 330 having gear teeth 335 .
- Contained in handle 250 is the cavity 350 for receiving pinion gear member 270 , having teeth 275 .
- Pinion gear member 270 is pivotally mounted in cavity 350 by pivot pins 265 . Teeth 275 mesh with and are engaged by teeth 335 . Extending out from pinion gear member 270 on the opposite side of pins 265 is the actuation trigger 280 . Actuation of trigger 280 will move tube 220 proximally and distally with respect to tube 240 . Actuating the trigger 280 will allow the stent 10 to be released from the tubes 220 and 240 .
- the stent and distal end of the instrument 200 are inserted into the urethra 410 through the meatus 400 of the patient's penis as seen in FIGS. 8 and 9.
- the distal end of the instrument 200 and the stent 10 are manipulated through the urethra 410 such that the prostatic section of the stent is located within the prostatic urethra 411 and the distal end of the stent is distal to the external sphincter 430 , thereby providing an open passage for urine from bladder 450 through the lumen of the urethra.
- the application instrument 200 is withdrawn from the urethra 410 by engaging trigger 260 and pulling distally on the instrument, thereby completing the procedure and providing for an implanted stent 10 which allows for patency of the urethral lumen 410 .
- the stent 10 after having been in place for the appropriate period of time has been converted into a state wherein it is substantially a soft, flexible filament, and is readily passed from the urethra 410 out of the patient's body with the urine flow, or is manually pulled out of the lumen. It will be appreciated by those skilled in the art that placement for other types of body lumens could be done in a similar manner, with modification as required by the unique characteristics of the lumen or of the surgical emplacement procedure.
- a polydioxanone homopolymer was added to a nitrogen purged hopper of a 3 ⁇ 4′′ vertical single screw extruder with a 24:1 L:D standard screw.
- the temperature profile of the extruder was 250°, 260°, 270° and 275° F. from rear zone to die.
- the screw speed was 6.5 RPM and the adapt pressure was 1345 psi.
- a B&H 25 cross head was employed with a 20 mil diameter guider (pressure tip) and a 48 mil diameter die.
- a spool of Vicryl brand suture, available from Ethicon, Inc., Somerville, N.J., with 18 mil diameter on a pay-off was guided through the guider inside the cross head, then coated by polydioxanone molt, chilled in a water trough, dried by a air wiper, took off and spooled sequentially.
- the temperature of the water trough was 8° C.
- the take-off speed was 2.1 M/min.
- the fiber with the O.D. of 44 mil was made and stored in nitrogen environment.
- Example 1 The coated suture of Example 1 was tied so that it created a small loop through the first hole C of the mandrel (see FIG. 10). Two metal posts ( ⁇ 2 ⁇ 15 mm length) are inserted into the holes A and B.
- a post was located at hole A and B. Clamp the C-side end of the mandrel to a winding motor. The 5-foot long fiber was cut from the spool and passed through the loop. The two free ends were held together and the folded fiber was stretched loosely so that the loop was positioned to be in the approximate center of the fiber. The fiber was loosely hold by two figures as a guide to make sure that the coils are packed closely together. A winder was run between 20-30 RPM for the length of the Prostatic Section.
- the coiling start from point C. Once the first post (B) was reached, the fiber was then bent over the post at an angle toward the distal section. Winding 180° more to form the connector, the fiber reached toward the second post (A), and then past it. The fiber is pulled back to a perpendicular position to the mandrel and the distal loop is then coiled. A wire tie was used to secure the fiber onto the mandrel. The assembly was stored under vacuum for 48 hours to allow it to dry prior to annealing.
- the posts Prior to annealing, the posts were removed from the mandrel. The entire assembly was hanged in annealing over and annealed at 80° C. for 10 hours. The stent was removed from the mandrel and stored in nitrogen box.
- a male patient is appropriately anesthetized and undergoes a prostrate thermal ablation procedure using conventional laser treatment devices.
- a stent 10 of the present invention is inserted into the patient's urethra and bladder in the following manner using an applicator 200 .
- the surgeon trims the stent to size.
- the stent is placed at the end of the applicator.
- a conventional scope is inserted into the lumen of the applicator.
- the stent and applicator are lubricated with a water soluble medical grade lubricant.
- a fluid reservoir is attached to the applier as in any standard cystoscopy procedure.
- the stent is placed in the prostatic urethra under direct visualization using a scope.
- the applier is removed, leaving behind the stent in the prostatic urethra.
- the outer coating absorbs and or degrades, thereby converting the stent into a soft, flexible filamentary structure that is removed from the urinary tract by grasping the end of the filament and pulling it from the lumen.
- the stents of the present invention provide many advantages over the stents of the prior art.
- the advantages include: rigidity (lumen patency) for a prescribed time; a degradation/absorption softening mechanism, whereby the stent softens into a readily passable/removable filament; biocompatibility; means to prevent migration; means to non-invasively monitor the stent and its position by X-ray. etc.
Abstract
A removable stent for implantation into a lumen in a human body. The stent is made from a soft, flexible fiber having an outer surface. An outer bioabsorbable/degradable coating is applied to the outer surface of the filament causing it to become rigid. The coating softens in vivo through absorption and/or degradation such that the stent is readily passed or removed from the lumen as a softened filament after a pre-determined period of time through normal flow of body fluids passing through the lumen or by manual removal.
Description
- The field of art to which this invention relates is medical devices, in particular, removable stent devices having bioabsorbable or biodegradable polymer coatings.
- The use of stent medical devices, or other types of endoluminal mechanical support devices, to keep a duct, vessel or other body lumen open in the human body has developed into a primary therapy for lumen stenosis or obstruction. The use of stents in various surgical procedures has quickly become accepted as experience with stent devices accumulates, and the number of surgical procedures employing them increases as their advantages become more widely recognized. For example, it is known to use stents in body lumens in order to maintain open passageways such as the prostatic urethra, the esophagus, the biliary tract, intestines, and various coronary arteries and veins, as well as more remote cardiovascular vessels such as the femoral artery, etc. There are two types of stents that are presently utilized: permanent stents and temporary stents. A permanent stent is designed to be maintained in a body lumen for an indeterminate amount of time. Temporary stents are designed to be maintained in a body lumen for a limited period of time in order to maintain the patency of the body lumen, for example, after trauma to a lumen caused by a surgical procedure or an injury. Permanent stents are typically designed to provide long term support for damaged or traumatized wall tissues of the lumen. There are numerous conventional applications for permanent stents including cardiovascular, urological, gastrointestinal, and gynecological applications.
- It is known that permanent stents, over time, become encapsulated and covered with endothelium tissues, for example, in cardiovascular applications. Similarly, permanent stents are known to become covered by epithelium, for example, in urethral applications. Temporary stents, on the other hand are designed to maintain the passageway of a lumen open for a specific, limited period of time, and preferably do not become incorporated into the walls of the lumen by tissue ingrowth or encapsulation. Temporary stents may advantageously be eliminated from body lumens after a predetermined, clinically appropriate period of time, for example, after the traumatized tissues of the lumen have healed and a stent is no longer needed to maintain the patency of the lumen. For example, temporary stents can be used as substitutes for in-dwelling catheters for applications in the treatment of prostatic obstruction or other urethral stricture diseases. Another indication for temporary stents in a body lumen is after energy ablation, such as laser or thermal ablation, or irradiation of prostatic tissue, in order to control post-operative acute urinary retention or other body fluid retention.
- It is known in the art to make both permanent and temporary stents from various conventional, biocompatible metals. However, there are several disadvantages that may be associated with the use of metal stents. For example, it is known that the metal stents may become encrusted, encapsulated, epithelialized or ingrown with body tissue. The stents are known to migrate on occasion from their initial insertion location. Such stents are known to cause irritation to the surrounding tissues in a lumen. Also, since metals are typically much harder and stiffer than the surrounding tissues in a lumen, this may result in an anatomical or physiological mismatch, thereby damaging tissue or eliciting unwanted biologic responses. Although permanent metal stents are designed to be implanted for an indefinite period of time, it is sometimes necessary to remove permanent metal stents. For example, if there is a biological response requiring surgical intervention, often the stent must be removed through a secondary procedure. If the metal stent is a temporary stent, it will also have to be removed after a clinically appropriate period of time. Regardless of whether the metal stent is categorized as permanent or temporary, if the stent has been encapsulated, epithelialized, etc., the surgical removal of the stent will resultingly cause undesirable pain and discomfort to the patient and possibly additional trauma to the lumen tissue. In addition to the pain and discomfort, the patient must be subjected to an additional time consuming and complicated surgical procedure with the attendant risks of surgery, in order to remove the metal stent.
- Similar complications and problems, as in the case of metal stents, may well result when using permanent stents made from non-absorbable biocompatible polymer or polymer-composites although these materials may offer certain benefits such as reduction in stiffness.
- It is known to use bioabsorbable and biodegradable materials for manufacturing temporary stents. The conventional bioabsorbable or bioresorbable materials from which such stents are made are selected to absorb or degrade over time, thereby eliminating the need for subsequent surgical procedures to remove the stent from the body lumen. In addition to the advantages attendant with not having to surgically remove such stents, it is known that bioabsorbable and biodegradable materials tend to have excellent biocompatibility characteristics, especially in comparison to most conventionally used biocompatible metals in certain sensitive patients. Another advantage of stents made from bioabsorbable and biodegradable materials is that the mechanical properties can be designed to substantially eliminate or reduce the stiffness and hardness that is often associated with metal stents, which can contribute to the propensity of a stent to damage a vessel or lumen.
- However, there are disadvantages and limitations known to be associated with the use of bioabsorbable or biodegradable stents. The limitations arise from the characteristics of the materials from which such stents are made. One of the problems associated with the current stents is that the materials break down too quickly. This improper breakdown or degradation of a stent into large, rigid fragments in the interior of a lumen, such as the urethra, may cause obstruction to normal flow, such as voiding, thereby interfering with the primary purpose of the stent in providing lumen patency. Alternatively, they take a long time to breakdown and stay in the target lumen for a considerable period of time after their therapeutic use has been accomplished. There is thus a long-term risk associated with these materials to form stones when uretheral stents made from longer degrading biodegradable polymers.
- Accordingly, there is a need in this art for novel, temporary stents, wherein the stents remain functional in a body lumen for the duration of a prescribed, clinically appropriate period of time to accomplish the appropriate therapeutical purpose, and, then soften and are removable as an elongated string-like member without producing fragments, which may cause irritation, obstruction, pain or discomfort to the patient, and without the need for a surgical procedure.
- In a preferred embodiment of the present invention, the temporary stent readily passes out of the body, or is removed as, a limp, flexible string-like member, and irritation, obstruction, pain or discomfort to the patient is either eliminated, or if present, is minimal.
- It is an object of the present invention to provide a stent for insertion into a body lumen which is manufactured from a flexible filament member, such as a suture, and then coated with a biodegradable or bioabsorbale polymer such that the member is formed into a relatively rigid stent, and when in the body, softens back into a flexible filament member which is easily passed or removed from the body lumen after a specific therapeutic period of time.
- Therefore, an implantable stent is disclosed for use in body lumens, wherein such lumens exist as part of the natural anatomy or are made surgically. The stent is an elongate, hollow member having a helical or coiled structure, and in a preferred embodiment has a helical structure having a plurality of coils. The structure has a longitudinal axis and a longitudinal passage. The coils have a pitch. The structure is made from a flexible, limp filament or fiber, such as a surgical suture, having an exterior polymeric coating. The polymeric coating is a bioabsorbable or biodegradable polymer, or blend thereof. At body temperature, the coating is solid, and of sufficient thickness to effectively cause the flexible, limp member to be maintained in a substantially rigid, fixed state as a structure. The rate of degradation or absorption of the coating in vivo is sufficient to effectively soften or be removed from the outer surface of the filament within the desired therapeutic period. This effectively provides that as the coating degrades, softens or is absorbed in vivo, it loses its mechanical integrity. This allows the filament to revert to its natural, flexible limp state, causing the stent structure to effectively collapse, and the filament may be removed or eliminated from the lumen.
- Upon in vivo exposure to body fluids, the progressively degrading and/or absorbing coating causes the stent to soften and collapse into a flexible filament that can readily pass out of the body lumen, either by manipulation or through natural expulsion with body fluids, thereby minimizing the possibility of causing obstruction, pain or discomfort.
- Yet another aspect of the present invention is the above-described stent made from a fiber which is radio-opaque.
- Yet another aspect of the present invention is a method of using the stents of the present invention in a surgical procedure to maintain the patency of a body lumen. A stent of the present invention is provided. The stent is an elongate, hollow member and in a preferred embodiment has a helical structure having a plurality of coils. The member has a longitudinal axis. The coils have a pitch. The structure is made from a flexible, limp filament or a fiber, having an outer surface and an exterior polymeric coating. The stent is inserted into a body lumen. The exposure to in vivo body fluids causes the exterior coating to absorb and/or degrade and soften, thereby causing the stent structure to collapse and return to a limp, flexible filament that can then be either eliminated by the passage of body fluids or manually removed.
- These and other aspects of the present invention will become more apparent from the following description and examples, and accompanying drawings.
- FIG. 1 is a perspective view of a preferred embodiment of a stent device of the present invention mounted to the distal end of an applicator instrument.
- FIG. 2 is a perspective view of the stent and applicator of FIG. 1, prior to loading the stent onto the applicator instrument.
- FIG. 3 is a side view of a stent device of the present invention, having a helical configuration.
- FIG. 4 is a cross-sectional view of the fiber used to make the stent of FIG. 3 taken along View Line4-4 illustrating a circular cross-section.
- FIG. 5 is a side view of the stent and applicator device of FIG. 1, where the device is shown in the ready position, prior to application.
- FIG. 6 is a side view of the stent and applicator device of FIG. 5, illustrating the position of the stent relative to the applicator when the stent is partially deployed by engaging the applicator trigger.
- FIG. 7 illustrates the relative positions of the stent to the applicator of FIG. 6 when the stent is fully deployed by fully engaging the applicator trigger.
- FIG. 8 illustrates the stent of the present invention fully deployed in the urethra and prostate of a patient, providing for a patent lumen.
- FIG. 9 illustrates a stent of the present invention emplaced in the urethra of a patient after the coating has degraded, been absorbed or otherwise broken down or softened; showing the stent being removed from the body as an elongated, soft, flexible filament.
- FIG. 10 is a schematic of a mandrel used to manufacture stents in Example 3.
- Referring to FIGS.1-9, a preferred embodiment of a stent of the present invention is illustrated. As seen in FIG. 3, the
stent 10 is seen to be a helical structure having a series of connected coils 20. The coils are made fromfilament 100. The term filament as used herein is defined to include not only filaments but fibers as well, and is used interchangeably with the term fiber. It is preferred thatfilament 100 be a continuous filament, however, it is possible to makestent 10 from two or more sections of filament which are subsequently connected or hinged together. As seen in FIG. 4, thefilament 100 is seen to have innerflexible member 110 andouter coating 130. The innerflexible member 110 is seen to haveouter surface 115. Covering theouter surface 115 offlexible member 110 is theouter coating 130.Outer coating 130 is seen to haveinner surface 135 andexterior surface 140. Preferably,inner surface 135 is in contact with, and affixed to, theouter surface 115. The stent is seen to have alongitudinal axis 70, and internal passageway 11. Thestent 10 is seen to have a firstdistal section 30 ofcoils 20 connected to asecond section 50 ofcoils 20, wherein thesections fiber 60. Thedistal section 30 of coils adjacent to hinged connectingfiber 60 forms an anchoring section which is inserted distal to the external sphincter. Theproximal section 50 of thestent 10 is maintained within the prostatic urethra.Proximal section 50 is seen to havecoils 20 havingdiameter 24, and also haspassageway 51. Thedistal section 30 ofstent 10 hascoils 20 having adiameter 22.Distal section 30 also has apassageway 31.Passage ways stent 10. As seen in FIG. 4, one preferred embodiment of thestent 10 of the present invention has afilament 100 having a circular cross-sectional configuration. Thefilament 100 may have various configurations depending upon the application including round, square, polygonal, curved, oval, and combinations thereof and equivalents thereof. Those skilled in the art will appreciate that certain cross-sectional configurations will provide different advantages in the stent. For example, the advantages of fiber of the present invention having a round cross-section include ease of the stent manufacturing process due to a possible on-line, one-step transition from the fiber to the stent in future manufacturing processes, flexibility during the stent deployment by being able to tailor the length of the stent during a surgical procedure to fit a particular patient's anatomy, and the use of commercially available filaments such as sutures. - The
stent 10 is preferably manufactured from a flexible,polymeric filament 100 having a desired cross-sectional configuration. The length and overall diameter of thestent 10 will depend upon a number of factors including the anatomy of the patient, the size of the anatomy and the type of surgical procedure which has effected the urethral lumen. For example, the overall length of astent 10 useful in the practice of the present invention will be sufficient to effectively maintain the lumen passage open. Typically the length for urethral applications in and adult male, the length will be about 10 mm to about 200 mm, more typically about 20 mm to about 100 mm, and preferably about 40 mm to about 80 mm. The diameter of astent 10 of the present invention will be sufficient to effectively maintain patency of the lumen. For prostatic urethral applications, where the stent has two sections having different diameters, typically the diameter in the prostatic urethra will typically be about 2 mm to about 25 mm, more typically about 4 mm to about 15 mm, and preferably about 6 mm to about 10 mm. The diameter of the section used to anchor distal to the external sphincter will be about 2 mm to about 25 mm, more typically about 4 mm to about 15 mm, and preferably about 6 mm to about 10 mm. The major cross-sectional dimension of a fiber used to manufacture a stent of the present invention will be sufficient to provide effective support and flexibility. Typically, when utilizing a circular cross-section, the diameter for urethral applications will be about 0.1 mm to about 4 mm, more typically about 0.5 mm to about 3 mm, and preferably about 1 mm to about 2 mm. The pitch, length, diameter and fiber diameter of the stents of the present invention will be sufficient to effectively provide sufficient support in response to radial stress of the urethral vessel walls, while providing for ease of insertion and stability while inserted in the urethral lumen, as well as desired flexibility and lumen patency. The pitch of the stent is defined to be the number of coils per unit length. In this patent application specification, for this example, pitch is defined as the number of coils per centimeter of stent length. Typically, for urethral applications, the pitch will be about 2.5 to about 100, more typically about 3 to about 20, and preferably about 5 to about 10. Although it is preferred for urethral applications that there be no space between adjacent coils, the stents of the present invention may have spaces between adjacent coils. - The
flexible members 110 coated withcoatings 130 to formfilaments 100 of the present invention will preferably be selected to have sufficient flexibility and softness and limpness to effectively provide for a stent that will collapse and be easily removed from a body lumen. The materials useful for the flexible member include flexible, limp monofilament and braided string-like members. It is particularly preferred to use conventional nonabsorbable sutures, such as monofilament or braided polypropylene, silk, polyester, nylon and the like and equivalents thereof. The flexible members may also be conventional absorbable sutures, monofilament or braided, including 95/5 lactide/glycolide, and polydioxanone, and the like. Theflexible member 110 may also be made from yarn type materials made from biocompatible fibers that are “spun” together to form the yarn. - The outer coatings useful for the stents and filaments of the present invention will be conventional biodegradable or bioabsorbable polymers, and blends thereof, including polymers made from monomers selected from the group consisting of lactide, glycolide, para-dioxanone, caprolactone, and trimethylene carbonate, caprolactone, blends thereof and copolymers thereof. The effect of the degradation or absorption of the polymeric coating is to convert the filament back into a soft, flexible member after a predetermined time period, such that the stent effectively collapses, and the flexible member can then be easily removed or passed from the lumen. In a flow environment, the progressively degrading stent can readily pass through the body or be removed from the lumen without causing obstruction. The types of polymeric coatings that can advantageously provide stiffness to form a
filament 100 include polymers with glass transition temperatures above room temperature and preferably above 55° C., and most preferably above about 120° C. These materials may be amorphous, that is, not display crystallinity. Polymers that have glass transition temperatures that are low, especially below room temperature, will generally require some crystallinity to provide the dimensional stability and stiffness to function in the present application. These can be described as semicrystalline. Regarding water soluble polymers for the coating, there are two general classes of water soluble polymers: ionic and non-ionic. In general of use are polyacrylamides, polyacrylic acid polymers, polyethers (especially the polyethylene glycols or polyethylene oxides), vinyl polymers such as some polyvinyl alcohols and some poly(N-vinyl pyrrolidone)s. Certain polysaccharide gums may also be useful; certain hydroxy celluloses, such as hydroxy methyl cellulose or certain hydroxy isopropyl cellulose are also useful. - One can control the dissolution process by material selection. Altering molecular weight of the water soluble resin also provides a means of control.
- One can control the dissolution process by material selection. Altering molecular weight of the water soluble resin also provides a means of control.
- Utilization of polymer blending is particularly advantageous to achieve the necessary rates of dissolution. Polyamide (nylon) may be used as a component to advantage because it can provide mechanical strength, absorbs some water, etc.
- A possible preferred blend component is polyethylene glycol (PEG or polyethylene oxide, PEO), especially those higher molecular weight resins that are semicrystalline. The melting point of PEG is about 60° C., which is high enough to meet requirements of a coating useful in the present invention. Optionally, the PEO may be blended with nylon. In addition, biodegradable polymers made from poly glycolide/lactide copolymers, polycaprolactone, and the like may be used for the outer coating of the
filament 100. In addition, polyoxaesters can be utilized which are water soluble and degrade by hydrolysis. Other suitable polymers are found in U.S. Pat. No. 5,980,551, which is incorporated by reference. - A stent must be designed to withstand radial stresses in order to perform its function of maintaining a passage through a lumen open. The mechanical capability of the stents of the present invention to withstand radial stresses when the stent is emplaced in the body lumen is provided primarily by the biodegradable/bioabsorbable material in the outer coating. The strength and stiffness and thickness of this material in the outer coating is sufficient to be effectively withstand the loads necessary to keep the stent functional. As the coating degrades and breaks down, it will have a sufficient thickness of properly selected biodegradable material to effectively be able to withstand the load necessary for the time period required to keep the lumen patent. In essence then, the coating can be designed to fulfill the mechanical requirements of keeping the body lumen patent or open for the specific therapeutic time period.
- After the coating has degraded/absorbed and effectively been removed from the stent structure by body fluids, the remaining filament returns to its soft, pliable, fibrillar state as a flexible member. The remaining soft filament is readily excreted or removed from the lumen.
- The coated filaments of the present invention may be made by conventional processes including co-extrusion, melt coating, solution coating or powder coating followed by spreading the coating by melting, etc., and the like. For example, when using a coating process, the inner flexible member can be a mono-filament extruded material or can be made from a multi-filament braid. The outer coating can be added on top of the flexible member either by melt coating or solution coating by passing the inner core through a bath, through coating rollers, brushes, spraying and/or a die.
- In another embodiment of the present invention, the polymers and blends that are used to form the coating can be used as a drug delivery matrix. To form this matrix, the coating material would be mixed with a therapeutic agent. The variety of different therapeutic agents that can be used in conjunction with the polymers of the present invention is vast. In general, therapeutic agents which may be administered via the pharmaceutical compositions of the invention include, without limitation: anti-infectives such as antibiotics and anti-viral agents; analgesics and analgesic combinations; anti-inflammatory agents; hormones such as steroids; bone regenerating growth factors; and naturally derived or genetically engineered proteins, polysaccharides, glycoproteins, or lipoproteins.
- Matrix formulations may be formulated by mixing one or more therapeutic agents with the polymer. The therapeutic agent, may be present as a liquid, a finely divided solid, or any other appropriate physical form. Typically, but optionally, the matrix will include one or more additives, such as diluents, carriers, excipients, stabilizers or the like.
- The amount of therapeutic agent will depend on the particular drug being employed and medical condition being treated. Typically, the amount of drug represents about 0.001 percent to about 70 percent, more typically about 0.001 percent to about 50 percent, most typically about 0.001 percent to about 20 percent by weight of the matrix. The quantity and type of polymer incorporated into the drug delivery matrix will vary depending on the release profile desired and the amount of drug employed.
- Upon contact with body fluids, the polymer coating undergoes gradual degradation (mainly through hydrolysis) or absorption with concomitant release of the dispersed drug for a sustained or extended period. This can result in prolonged delivery (over, say 1 to 5,000 hours, preferably 2 to 800 hours) of effective amounts (say, 0.0001 mg/kg/hour to 10 mg/kg/hour) of the drug. This dosage form can be administered as is necessary depending on the subject being treated, the severity of the affliction, the judgment of the prescribing physician, and the like. Following this or similar procedures, those skilled in the art will be able to prepare a variety of formulations.
- The
stents 10 of the present invention when made from thecoated filament 100 may be manufactured in the following manner using a winding process. Afilament 100 is wound about a mandrel by heating thefilament 100 and then coiling it around the mandrel. The assembly of the mandrel and the coil are annealed under constraint and then the mandrel is removed. The pitch and diameter of the coils are selected to provide the desired size and shape of stent. If desired, thefilament 100 may be wound about the mandrel without heat, for example immediately upon entering a coating bath or melt bath, or the uncoatedflexible member 110 can be wound about a mandrel, and then the coating can be applied in a conventional manner, and cured as necessary. - The stents of the present invention may be utilized in the following manner in urethral stent placement procedures as illustrated in FIGS. 1, 2,5, 6, 7 and 8. Initially a
stent 10 is placed upon the distal end of anapplicator instrument 200.Instrument 200 is seen to havehandle 250 havinggrip 255. At the top 257 of thehandle 250 is mounted theshaft retention member 290.Retention member 290 is seen to havelongitudinal passageway 292,front 295 and back 296. The mountingtube 240 is seen to havedistal end 242 andproximal end 244. Mountingtube 240 is seen to havepassage 248. Theproximal end 244 oftube 240 is seen to be mounted inpassage way 292 such that theinner passageway 248 is in communication withpassageway 292. Slidably mounted inpassageway 248 is theapplicator tube 220.Tube 220 hasdistal end 222,proximal end 224, andpassageway 226. Mounted to theproximal end 224 oftube 220 is the mountingblock 300, which is affixed to end 224 bypin 309. Mounted to the bottom ofblock 300 israck gear member 330 havinggear teeth 335. Contained inhandle 250 is thecavity 350 for receivingpinion gear member 270, havingteeth 275.Pinion gear member 270 is pivotally mounted incavity 350 by pivot pins 265.Teeth 275 mesh with and are engaged byteeth 335. Extending out frompinion gear member 270 on the opposite side ofpins 265 is theactuation trigger 280. Actuation oftrigger 280 will movetube 220 proximally and distally with respect totube 240. Actuating thetrigger 280 will allow thestent 10 to be released from thetubes - The stent and distal end of the
instrument 200 are inserted into theurethra 410 through themeatus 400 of the patient's penis as seen in FIGS. 8 and 9. The distal end of theinstrument 200 and thestent 10 are manipulated through theurethra 410 such that the prostatic section of the stent is located within theprostatic urethra 411 and the distal end of the stent is distal to theexternal sphincter 430, thereby providing an open passage for urine frombladder 450 through the lumen of the urethra. Then, theapplication instrument 200 is withdrawn from theurethra 410 by engaging trigger 260 and pulling distally on the instrument, thereby completing the procedure and providing for an implantedstent 10 which allows for patency of theurethral lumen 410. As seen in FIG. 9, thestent 10 after having been in place for the appropriate period of time has been converted into a state wherein it is substantially a soft, flexible filament, and is readily passed from theurethra 410 out of the patient's body with the urine flow, or is manually pulled out of the lumen. It will be appreciated by those skilled in the art that placement for other types of body lumens could be done in a similar manner, with modification as required by the unique characteristics of the lumen or of the surgical emplacement procedure. - The following examples are illustrative of the principles and practice of the present invention, although not limited thereto.
- Manufacture of Filament Having Absorbable Coating by Extrusion Coating Process.
- A polydioxanone homopolymer was added to a nitrogen purged hopper of a ¾″ vertical single screw extruder with a 24:1 L:D standard screw. The temperature profile of the extruder was 250°, 260°, 270° and 275° F. from rear zone to die. The screw speed was 6.5 RPM and the adapt pressure was 1345 psi. A B&H25 cross head was employed with a 20 mil diameter guider (pressure tip) and a 48 mil diameter die. A spool of Vicryl brand suture, available from Ethicon, Inc., Somerville, N.J., with 18 mil diameter on a pay-off was guided through the guider inside the cross head, then coated by polydioxanone molt, chilled in a water trough, dried by a air wiper, took off and spooled sequentially. The temperature of the water trough was 8° C. The take-off speed was 2.1 M/min. The fiber with the O.D. of 44 mil was made and stored in nitrogen environment.
- Manufacture of Stent Using the Coated Filament
- The coated suture of Example 1 was tied so that it created a small loop through the first hole C of the mandrel (see FIG. 10). Two metal posts (φ2×15 mm length) are inserted into the holes A and B.
- A post was located at hole A and B. Clamp the C-side end of the mandrel to a winding motor. The 5-foot long fiber was cut from the spool and passed through the loop. The two free ends were held together and the folded fiber was stretched loosely so that the loop was positioned to be in the approximate center of the fiber. The fiber was loosely hold by two figures as a guide to make sure that the coils are packed closely together. A winder was run between 20-30 RPM for the length of the Prostatic Section.
- The coiling start from point C. Once the first post (B) was reached, the fiber was then bent over the post at an angle toward the distal section. Winding 180° more to form the connector, the fiber reached toward the second post (A), and then past it. The fiber is pulled back to a perpendicular position to the mandrel and the distal loop is then coiled. A wire tie was used to secure the fiber onto the mandrel. The assembly was stored under vacuum for 48 hours to allow it to dry prior to annealing.
- Prior to annealing, the posts were removed from the mandrel. The entire assembly was hanged in annealing over and annealed at 80° C. for 10 hours. The stent was removed from the mandrel and stored in nitrogen box.
- A male patient is appropriately anesthetized and undergoes a prostrate thermal ablation procedure using conventional laser treatment devices. After successful completion of the surgical procedure, a
stent 10 of the present invention is inserted into the patient's urethra and bladder in the following manner using anapplicator 200. The surgeon trims the stent to size. The stent is placed at the end of the applicator. A conventional scope is inserted into the lumen of the applicator. The stent and applicator are lubricated with a water soluble medical grade lubricant. A fluid reservoir is attached to the applier as in any standard cystoscopy procedure. The stent is placed in the prostatic urethra under direct visualization using a scope. Once positioned correctly, the applier is removed, leaving behind the stent in the prostatic urethra. In approximately 28 days after implantation, the outer coating absorbs and or degrades, thereby converting the stent into a soft, flexible filamentary structure that is removed from the urinary tract by grasping the end of the filament and pulling it from the lumen. - The stents of the present invention provide many advantages over the stents of the prior art. The advantages include: rigidity (lumen patency) for a prescribed time; a degradation/absorption softening mechanism, whereby the stent softens into a readily passable/removable filament; biocompatibility; means to prevent migration; means to non-invasively monitor the stent and its position by X-ray. etc.
- Although this invention has been shown and described with respect to detailed embodiments thereof, it will be understood by those skilled in the art that various changes in form and detail may be made without departing from the spirit and scope of the claimed invention.
Claims (27)
1. A stent, comprising:
a helical structure having a plurality of coils, said structure having a longitudinal axis and said coils having a pitch, said structure having an internal longitudinal passage wherein said structure is made from a filament having a cross-section and an outer surface, said filament comprising:
a soft flexible elongated member having an outer surface; and
a bioabsorbable or biodegradable polymeric outer coating on the outer surface of the member;
wherein, the polymeric coating has sufficient mechanical integrity to effectively maintain the flexible member in a helical configuration, until the coating has sufficiently been degraded or absorbed in vivo to effectively convert the helical structure back into a soft, elongated member.
2. The stent of claim 1 wherein the coating comprises a melt polymer.
3. The stent of claim 1 , wherein the coating comprises a solution polymer.
4. The stent of claim 1 wherein the filament comprises a surgical suture.
5. The stent of claim 4 , wherein the suture comprises a monofilament.
6. The stent of claim 4 , wherein the suture comprises a multifilament.
7. The stent of claim 4 , wherein the suture comprises a non-absorbable suture.
8. The stent of claim 4 wherein the suture comprises an absorbable suture.
9. The stent of claim 1 , wherein the coating comprises a polymer made from monomers selected from the group consisting of lactide, glycolide, para-dioxanone, caprolactone, and trimethylene carbonate, caprolactone, blends thereof and copolymers thereof
10. The stent of claim 1 , wherein the polymer of the coating has a glass transition temperature above 55 C.
11. The stent of claim 1 wherein the polymer of the coating has a glass transition temperature above 120 C.
12. The stent of claim 1 , wherein the polymeric coating comprise a polymer selected from the group consisting of polyacrylamides, polyethylene glycols, polyethylene oxide, vinyl alcohols, and poly(N-vinyl pyrrolidones.
13. The stent of claim 1 , wherein the polymeric coating additionally comprises polyamide.
14. A biodegradable filament, the filament comprising:
an elongated, flexible member having a cross-section, and an outer surface; and,
a polymeric coating on said outer surface, said coating comprising a biodegradable or bioabsorbable polymer,
wherein, the polymeric coating has sufficient mechanical integrity to effectively maintain the flexible member in a substantially fixed configuration, until the coating has sufficiently been degraded or absorbed in vivo to effectively convert the structure back into a soft, elongated member.
15. The stent of claim 9 wherein the coating comprises a melt polymer.
16. The stent of claim 9 , wherein the coating comprises a solution polymer.
17. The stent of claim 9 wherein the filament comprises a surgical suture.
18. The stent of claim 12 , wherein the suture comprises a monofilament.
19. The stent of claim 12 , wherein the suture comprises a multifilament.
20. The stent of claim 12 , wherein the suture comprises a non-absorbable suture.
21. The stent of claim 12 wherein the suture comprises an absorbable suture.
22. The stent of claim 1 , wherein the coating comprises a polymer made from monomers selected from the group consisting of lactide, glycolide, para-dioxanone, caprolactone, and trimethylene carbonate, caprolactone, blends thereof and copolymers thereof
23. The stent of claim 1 , wherein the polymer of the coating has a glass transition temperature above 55 C.
24. The stent of claim 1 wherein the polymer of the coating has a glass transition temperature above 120 C.
25. The stent of claim 1 , wherein the polymeric coating comprise a polymer selected from the group consisting of polyacrylamides, polyethylene glycols, polyethylene oxide, vinyl alochols, and poly(N-vinyl pyrrolidones.
26. The stent of claim 1 , wherein the polymeric coating additionally comprises polyamide.
27. A method of maintaining a passageway of a body lumen substantially open, comprising the steps of:
providing a stent, said stent comprising:
a helical structure having a plurality of coils, said structure having a longitudinal axis and a longitudinal passage, and said coils having a pitch, wherein said structure is made from a fiber, said fiber having a cross-section and said filament comprising:
an elongated flexible, filament member, having an external surface and a cross-section; and,
a, polymeric outer coating on the surface of the member, wherein, the polymeric coating has sufficient mechanical integrity to effectively maintain the flexible member in a helical configuration; and,
implanting said stent in a body lumen and maintaining the stent in the body lumen for a sufficient period of time to effectively maintain the passageway of the lumen substantially open for a desired period of time until the exterior coating softens, thereby converting the stent structure into a soft, flexible filamentary structure.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
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US10/196,845 US20020177904A1 (en) | 1999-12-22 | 2002-07-16 | Removable stent for body lumens |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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US09/470,620 US6494908B1 (en) | 1999-12-22 | 1999-12-22 | Removable stent for body lumens |
US10/196,845 US20020177904A1 (en) | 1999-12-22 | 2002-07-16 | Removable stent for body lumens |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
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US09/470,620 Division US6494908B1 (en) | 1999-12-22 | 1999-12-22 | Removable stent for body lumens |
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US10/196,845 Abandoned US20020177904A1 (en) | 1999-12-22 | 2002-07-16 | Removable stent for body lumens |
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US09/470,620 Expired - Lifetime US6494908B1 (en) | 1999-12-22 | 1999-12-22 | Removable stent for body lumens |
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Cited By (93)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20020002399A1 (en) * | 1999-12-22 | 2002-01-03 | Huxel Shawn Thayer | Removable stent for body lumens |
US6733536B1 (en) * | 2002-10-22 | 2004-05-11 | Scimed Life Systems | Male urethral stent device |
US20050137716A1 (en) * | 2003-12-17 | 2005-06-23 | Yosef Gross | Implant and delivery tool therefor |
WO2006044396A2 (en) | 2004-10-13 | 2006-04-27 | Scimed Life Systems, Inc. | Composite stent with inner and outer stent elements and method of using the same |
US20080262609A1 (en) * | 2006-12-05 | 2008-10-23 | Valtech Cardio, Ltd. | Segmented ring placement |
US7651529B2 (en) | 2003-05-09 | 2010-01-26 | Boston Scientific Scimed, Inc. | Stricture retractor |
US7691078B2 (en) | 2001-05-22 | 2010-04-06 | Boston Scientific Scimed, Inc. | Draining bodily fluids with a stent |
US20100130815A1 (en) * | 2007-05-18 | 2010-05-27 | Prostaplant Ltd. | Intraurethral and extraurethral apparatus |
US20100161043A1 (en) * | 2008-12-22 | 2010-06-24 | Valtech Cardio, Ltd. | Implantation of repair chords in the heart |
US20100280604A1 (en) * | 2009-05-04 | 2010-11-04 | Valtech Cardio, Ltd. | Over-wire rotation tool |
US8092415B2 (en) | 2007-11-01 | 2012-01-10 | C. R. Bard, Inc. | Catheter assembly including triple lumen tip |
US8206371B2 (en) | 2003-05-27 | 2012-06-26 | Bard Access Systems, Inc. | Methods and apparatus for inserting multi-lumen split-tip catheters into a blood vessel |
US8241351B2 (en) | 2008-12-22 | 2012-08-14 | Valtech Cardio, Ltd. | Adjustable partial annuloplasty ring and mechanism therefor |
US8277502B2 (en) | 2009-10-29 | 2012-10-02 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US8292841B2 (en) | 2007-10-26 | 2012-10-23 | C. R. Bard, Inc. | Solid-body catheter including lateral distal openings |
US8353956B2 (en) | 2009-02-17 | 2013-01-15 | Valtech Cardio, Ltd. | Actively-engageable movement-restriction mechanism for use with an annuloplasty structure |
WO2013006298A3 (en) * | 2011-07-07 | 2013-03-28 | The Regents Of The University Of California | A bioactive spiral coil coating |
US8475525B2 (en) | 2010-01-22 | 2013-07-02 | 4Tech Inc. | Tricuspid valve repair using tension |
US8500939B2 (en) | 2007-10-17 | 2013-08-06 | Bard Access Systems, Inc. | Manufacture of split tip catheters |
US8690939B2 (en) | 2009-10-29 | 2014-04-08 | Valtech Cardio, Ltd. | Method for guide-wire based advancement of a rotation assembly |
US8696614B2 (en) | 2007-10-26 | 2014-04-15 | C. R. Bard, Inc. | Split-tip catheter including lateral distal openings |
US8715342B2 (en) | 2009-05-07 | 2014-05-06 | Valtech Cardio, Ltd. | Annuloplasty ring with intra-ring anchoring |
US8734467B2 (en) | 2009-12-02 | 2014-05-27 | Valtech Cardio, Ltd. | Delivery tool for implantation of spool assembly coupled to a helical anchor |
US8808227B2 (en) | 2003-02-21 | 2014-08-19 | C. R. Bard, Inc. | Multi-lumen catheter with separate distal tips |
US8858623B2 (en) | 2011-11-04 | 2014-10-14 | Valtech Cardio, Ltd. | Implant having multiple rotational assemblies |
US8926696B2 (en) | 2008-12-22 | 2015-01-06 | Valtech Cardio, Ltd. | Adjustable annuloplasty devices and adjustment mechanisms therefor |
US8940044B2 (en) | 2011-06-23 | 2015-01-27 | Valtech Cardio, Ltd. | Closure element for use with an annuloplasty structure |
US8961596B2 (en) | 2010-01-22 | 2015-02-24 | 4Tech Inc. | Method and apparatus for tricuspid valve repair using tension |
US8961594B2 (en) | 2012-05-31 | 2015-02-24 | 4Tech Inc. | Heart valve repair system |
US8992454B2 (en) * | 2004-06-09 | 2015-03-31 | Bard Access Systems, Inc. | Splitable tip catheter with bioresorbable adhesive |
US9011530B2 (en) | 2008-12-22 | 2015-04-21 | Valtech Cardio, Ltd. | Partially-adjustable annuloplasty structure |
US9011520B2 (en) | 2009-10-29 | 2015-04-21 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US9108017B2 (en) | 2011-03-22 | 2015-08-18 | Applied Medical Resources Corporation | Method of making tubing have drainage holes |
US9180007B2 (en) | 2009-10-29 | 2015-11-10 | Valtech Cardio, Ltd. | Apparatus and method for guide-wire based advancement of an adjustable implant |
USD748252S1 (en) | 2013-02-08 | 2016-01-26 | C. R. Bard, Inc. | Multi-lumen catheter tip |
US9241702B2 (en) | 2010-01-22 | 2016-01-26 | 4Tech Inc. | Method and apparatus for tricuspid valve repair using tension |
US9277994B2 (en) | 2008-12-22 | 2016-03-08 | Valtech Cardio, Ltd. | Implantation of repair chords in the heart |
US9307980B2 (en) | 2010-01-22 | 2016-04-12 | 4Tech Inc. | Tricuspid valve repair using tension |
US9351830B2 (en) | 2006-12-05 | 2016-05-31 | Valtech Cardio, Ltd. | Implant and anchor placement |
US9526613B2 (en) | 2005-03-17 | 2016-12-27 | Valtech Cardio Ltd. | Mitral valve treatment techniques |
US9579485B2 (en) | 2007-11-01 | 2017-02-28 | C. R. Bard, Inc. | Catheter assembly including a multi-lumen configuration |
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US9693865B2 (en) | 2013-01-09 | 2017-07-04 | 4 Tech Inc. | Soft tissue depth-finding tool |
US9724192B2 (en) | 2011-11-08 | 2017-08-08 | Valtech Cardio, Ltd. | Controlled steering functionality for implant-delivery tool |
US9730793B2 (en) | 2012-12-06 | 2017-08-15 | Valtech Cardio, Ltd. | Techniques for guide-wire based advancement of a tool |
US9801720B2 (en) | 2014-06-19 | 2017-10-31 | 4Tech Inc. | Cardiac tissue cinching |
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US9907547B2 (en) | 2014-12-02 | 2018-03-06 | 4Tech Inc. | Off-center tissue anchors |
US9907681B2 (en) | 2013-03-14 | 2018-03-06 | 4Tech Inc. | Stent with tether interface |
US9949828B2 (en) | 2012-10-23 | 2018-04-24 | Valtech Cardio, Ltd. | Controlled steering functionality for implant-delivery tool |
US9968452B2 (en) | 2009-05-04 | 2018-05-15 | Valtech Cardio, Ltd. | Annuloplasty ring delivery cathethers |
US10022114B2 (en) | 2013-10-30 | 2018-07-17 | 4Tech Inc. | Percutaneous tether locking |
US10039643B2 (en) | 2013-10-30 | 2018-08-07 | 4Tech Inc. | Multiple anchoring-point tension system |
US10052095B2 (en) | 2013-10-30 | 2018-08-21 | 4Tech Inc. | Multiple anchoring-point tension system |
US10058323B2 (en) | 2010-01-22 | 2018-08-28 | 4 Tech Inc. | Tricuspid valve repair using tension |
US10098737B2 (en) | 2009-10-29 | 2018-10-16 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
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US10258768B2 (en) | 2014-07-14 | 2019-04-16 | C. R. Bard, Inc. | Apparatuses, systems, and methods for inserting catheters having enhanced stiffening and guiding features |
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US10806579B2 (en) | 2017-10-20 | 2020-10-20 | Boston Scientific Scimed, Inc. | Heart valve repair implant for treating tricuspid regurgitation |
US10828160B2 (en) | 2015-12-30 | 2020-11-10 | Edwards Lifesciences Corporation | System and method for reducing tricuspid regurgitation |
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Families Citing this family (116)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8172897B2 (en) | 1997-04-15 | 2012-05-08 | Advanced Cardiovascular Systems, Inc. | Polymer and metal composite implantable medical devices |
US6240616B1 (en) | 1997-04-15 | 2001-06-05 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing a medicated porous metal prosthesis |
US10028851B2 (en) | 1997-04-15 | 2018-07-24 | Advanced Cardiovascular Systems, Inc. | Coatings for controlling erosion of a substrate of an implantable medical device |
US20070093889A1 (en) * | 1999-01-27 | 2007-04-26 | Wu Benjamin M | Non-Fragmenting Low Friction Bioactive Absorbable Coils for Brain Aneurysm Therapy |
US7169187B2 (en) * | 1999-12-22 | 2007-01-30 | Ethicon, Inc. | Biodegradable stent |
US6338739B1 (en) | 1999-12-22 | 2002-01-15 | Ethicon, Inc. | Biodegradable stent |
US8460367B2 (en) | 2000-03-15 | 2013-06-11 | Orbusneich Medical, Inc. | Progenitor endothelial cell capturing with a drug eluting implantable medical device |
US8088060B2 (en) | 2000-03-15 | 2012-01-03 | Orbusneich Medical, Inc. | Progenitor endothelial cell capturing with a drug eluting implantable medical device |
US9522217B2 (en) | 2000-03-15 | 2016-12-20 | Orbusneich Medical, Inc. | Medical device with coating for capturing genetically-altered cells and methods for using same |
US6743210B2 (en) * | 2001-02-15 | 2004-06-01 | Scimed Life Systems, Inc. | Stent delivery catheter positioning device |
US6685745B2 (en) | 2001-05-15 | 2004-02-03 | Scimed Life Systems, Inc. | Delivering an agent to a patient's body |
US6585754B2 (en) * | 2001-05-29 | 2003-07-01 | Scimed Life Systems, Inc. | Absorbable implantable vaso-occlusive member |
US7989018B2 (en) | 2001-09-17 | 2011-08-02 | Advanced Cardiovascular Systems, Inc. | Fluid treatment of a polymeric coating on an implantable medical device |
US7285304B1 (en) | 2003-06-25 | 2007-10-23 | Advanced Cardiovascular Systems, Inc. | Fluid treatment of a polymeric coating on an implantable medical device |
US6863683B2 (en) | 2001-09-19 | 2005-03-08 | Abbott Laboratoris Vascular Entities Limited | Cold-molding process for loading a stent onto a stent delivery system |
US20030153972A1 (en) * | 2002-02-14 | 2003-08-14 | Michael Helmus | Biodegradable implantable or insertable medical devices with controlled change of physical properties leading to biomechanical compatibility |
US20030153971A1 (en) * | 2002-02-14 | 2003-08-14 | Chandru Chandrasekaran | Metal reinforced biodegradable intraluminal stents |
US9307991B2 (en) | 2002-08-22 | 2016-04-12 | Ams Research, Llc | Anastomosis device and related methods |
US8551126B2 (en) | 2002-08-22 | 2013-10-08 | Ams Research Corporation | Anastomosis device and related methods |
US8764775B2 (en) | 2002-08-22 | 2014-07-01 | Ams Research Corporation | Anastomosis device and related methods |
US8435550B2 (en) | 2002-12-16 | 2013-05-07 | Abbot Cardiovascular Systems Inc. | Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device |
US7758881B2 (en) | 2004-06-30 | 2010-07-20 | Advanced Cardiovascular Systems, Inc. | Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device |
US20040199246A1 (en) * | 2003-04-02 | 2004-10-07 | Scimed Life Systems, Inc. | Expandable stent |
US7757691B2 (en) | 2003-08-07 | 2010-07-20 | Merit Medical Systems, Inc. | Therapeutic medical appliance delivery and method of use |
US7198675B2 (en) | 2003-09-30 | 2007-04-03 | Advanced Cardiovascular Systems | Stent mandrel fixture and method for selectively coating surfaces of a stent |
US7368169B2 (en) * | 2003-12-01 | 2008-05-06 | Rutgers, The State University Of New Jersey | Hydrazide compounds with angiogenic activity |
US20050131515A1 (en) | 2003-12-16 | 2005-06-16 | Cully Edward H. | Removable stent-graft |
US20050245938A1 (en) * | 2004-04-28 | 2005-11-03 | Kochan Jeffrey P | Method and apparatus for minimally invasive repair of intervertebral discs and articular joints |
US8568469B1 (en) | 2004-06-28 | 2013-10-29 | Advanced Cardiovascular Systems, Inc. | Stent locking element and a method of securing a stent on a delivery system |
US8241554B1 (en) | 2004-06-29 | 2012-08-14 | Advanced Cardiovascular Systems, Inc. | Method of forming a stent pattern on a tube |
US8747879B2 (en) | 2006-04-28 | 2014-06-10 | Advanced Cardiovascular Systems, Inc. | Method of fabricating an implantable medical device to reduce chance of late inflammatory response |
US8747878B2 (en) | 2006-04-28 | 2014-06-10 | Advanced Cardiovascular Systems, Inc. | Method of fabricating an implantable medical device by controlling crystalline structure |
US8778256B1 (en) | 2004-09-30 | 2014-07-15 | Advanced Cardiovascular Systems, Inc. | Deformation of a polymer tube in the fabrication of a medical article |
US7971333B2 (en) | 2006-05-30 | 2011-07-05 | Advanced Cardiovascular Systems, Inc. | Manufacturing process for polymetric stents |
US7731890B2 (en) | 2006-06-15 | 2010-06-08 | Advanced Cardiovascular Systems, Inc. | Methods of fabricating stents with enhanced fracture toughness |
US9283099B2 (en) | 2004-08-25 | 2016-03-15 | Advanced Cardiovascular Systems, Inc. | Stent-catheter assembly with a releasable connection for stent retention |
WO2006024489A2 (en) | 2004-08-30 | 2006-03-09 | Interstitial Therapeutics | Methods and compositions for the treatment of cell proliferation |
US7229471B2 (en) | 2004-09-10 | 2007-06-12 | Advanced Cardiovascular Systems, Inc. | Compositions containing fast-leaching plasticizers for improved performance of medical devices |
US8043553B1 (en) | 2004-09-30 | 2011-10-25 | Advanced Cardiovascular Systems, Inc. | Controlled deformation of a polymer tube with a restraining surface in fabricating a medical article |
US7875233B2 (en) | 2004-09-30 | 2011-01-25 | Advanced Cardiovascular Systems, Inc. | Method of fabricating a biaxially oriented implantable medical device |
US8173062B1 (en) | 2004-09-30 | 2012-05-08 | Advanced Cardiovascular Systems, Inc. | Controlled deformation of a polymer tube in fabricating a medical article |
US7632307B2 (en) * | 2004-12-16 | 2009-12-15 | Advanced Cardiovascular Systems, Inc. | Abluminal, multilayer coating constructs for drug-delivery stents |
US8636756B2 (en) | 2005-02-18 | 2014-01-28 | Ams Research Corporation | Anastomosis device and surgical tool actuation mechanism configurations |
DE102005016103B4 (en) * | 2005-04-08 | 2014-10-09 | Merit Medical Systems, Inc. | Duodenumstent |
US7381048B2 (en) | 2005-04-12 | 2008-06-03 | Advanced Cardiovascular Systems, Inc. | Stents with profiles for gripping a balloon catheter and molds for fabricating stents |
DE102005019649A1 (en) * | 2005-04-26 | 2006-11-02 | Alveolus Inc. | Flexible stent for positioning in lumen of esophagus comprises tube and stabilization members defined circumferentially about tube, where each member extends inwardly in tube to define inner diameter that is less than inner diameter of tube |
US7717928B2 (en) * | 2005-05-20 | 2010-05-18 | Ams Research Corporation | Anastomosis device configurations and methods |
US7771443B2 (en) | 2005-05-20 | 2010-08-10 | Ams Research Corporation | Anastomosis device approximating structure configurations |
US7658880B2 (en) | 2005-07-29 | 2010-02-09 | Advanced Cardiovascular Systems, Inc. | Polymeric stent polishing method and apparatus |
US9248034B2 (en) | 2005-08-23 | 2016-02-02 | Advanced Cardiovascular Systems, Inc. | Controlled disintegrating implantable medical devices |
US7867547B2 (en) | 2005-12-19 | 2011-01-11 | Advanced Cardiovascular Systems, Inc. | Selectively coating luminal surfaces of stents |
US20070156230A1 (en) | 2006-01-04 | 2007-07-05 | Dugan Stephen R | Stents with radiopaque markers |
US7951185B1 (en) | 2006-01-06 | 2011-05-31 | Advanced Cardiovascular Systems, Inc. | Delivery of a stent at an elevated temperature |
US7964210B2 (en) | 2006-03-31 | 2011-06-21 | Abbott Cardiovascular Systems Inc. | Degradable polymeric implantable medical devices with a continuous phase and discrete phase |
US8069814B2 (en) | 2006-05-04 | 2011-12-06 | Advanced Cardiovascular Systems, Inc. | Stent support devices |
US7761968B2 (en) | 2006-05-25 | 2010-07-27 | Advanced Cardiovascular Systems, Inc. | Method of crimping a polymeric stent |
US7951194B2 (en) | 2006-05-26 | 2011-05-31 | Abbott Cardiovascular Sysetms Inc. | Bioabsorbable stent with radiopaque coating |
US8752268B2 (en) | 2006-05-26 | 2014-06-17 | Abbott Cardiovascular Systems Inc. | Method of making stents with radiopaque markers |
US8343530B2 (en) | 2006-05-30 | 2013-01-01 | Abbott Cardiovascular Systems Inc. | Polymer-and polymer blend-bioceramic composite implantable medical devices |
US7842737B2 (en) | 2006-09-29 | 2010-11-30 | Abbott Cardiovascular Systems Inc. | Polymer blend-bioceramic composite implantable medical devices |
US7959940B2 (en) | 2006-05-30 | 2011-06-14 | Advanced Cardiovascular Systems, Inc. | Polymer-bioceramic composite implantable medical devices |
US20070282434A1 (en) * | 2006-05-30 | 2007-12-06 | Yunbing Wang | Copolymer-bioceramic composite implantable medical devices |
US8034287B2 (en) | 2006-06-01 | 2011-10-11 | Abbott Cardiovascular Systems Inc. | Radiation sterilization of medical devices |
US8486135B2 (en) | 2006-06-01 | 2013-07-16 | Abbott Cardiovascular Systems Inc. | Implantable medical devices fabricated from branched polymers |
US8603530B2 (en) | 2006-06-14 | 2013-12-10 | Abbott Cardiovascular Systems Inc. | Nanoshell therapy |
US8048448B2 (en) | 2006-06-15 | 2011-11-01 | Abbott Cardiovascular Systems Inc. | Nanoshells for drug delivery |
US8535372B1 (en) | 2006-06-16 | 2013-09-17 | Abbott Cardiovascular Systems Inc. | Bioabsorbable stent with prohealing layer |
US8333000B2 (en) | 2006-06-19 | 2012-12-18 | Advanced Cardiovascular Systems, Inc. | Methods for improving stent retention on a balloon catheter |
US8017237B2 (en) | 2006-06-23 | 2011-09-13 | Abbott Cardiovascular Systems, Inc. | Nanoshells on polymers |
US9072820B2 (en) | 2006-06-26 | 2015-07-07 | Advanced Cardiovascular Systems, Inc. | Polymer composite stent with polymer particles |
US8128688B2 (en) | 2006-06-27 | 2012-03-06 | Abbott Cardiovascular Systems Inc. | Carbon coating on an implantable device |
US7794776B1 (en) | 2006-06-29 | 2010-09-14 | Abbott Cardiovascular Systems Inc. | Modification of polymer stents with radiation |
US7740791B2 (en) | 2006-06-30 | 2010-06-22 | Advanced Cardiovascular Systems, Inc. | Method of fabricating a stent with features by blow molding |
US7823263B2 (en) | 2006-07-11 | 2010-11-02 | Abbott Cardiovascular Systems Inc. | Method of removing stent islands from a stent |
US7757543B2 (en) | 2006-07-13 | 2010-07-20 | Advanced Cardiovascular Systems, Inc. | Radio frequency identification monitoring of stents |
US7998404B2 (en) | 2006-07-13 | 2011-08-16 | Advanced Cardiovascular Systems, Inc. | Reduced temperature sterilization of stents |
US7794495B2 (en) | 2006-07-17 | 2010-09-14 | Advanced Cardiovascular Systems, Inc. | Controlled degradation of stents |
US7886419B2 (en) | 2006-07-18 | 2011-02-15 | Advanced Cardiovascular Systems, Inc. | Stent crimping apparatus and method |
US8016879B2 (en) | 2006-08-01 | 2011-09-13 | Abbott Cardiovascular Systems Inc. | Drug delivery after biodegradation of the stent scaffolding |
US9173733B1 (en) | 2006-08-21 | 2015-11-03 | Abbott Cardiovascular Systems Inc. | Tracheobronchial implantable medical device and methods of use |
US7923022B2 (en) | 2006-09-13 | 2011-04-12 | Advanced Cardiovascular Systems, Inc. | Degradable polymeric implantable medical devices with continuous phase and discrete phase |
US8066725B2 (en) * | 2006-10-17 | 2011-11-29 | Ams Research Corporation | Anastomosis device having improved safety features |
US7993264B2 (en) * | 2006-11-09 | 2011-08-09 | Ams Research Corporation | Orientation adapter for injection tube in flexible endoscope |
DE102006053752A1 (en) | 2006-11-13 | 2008-05-15 | Aesculap Ag & Co. Kg | Textile vascular prosthesis with coating |
US8277466B2 (en) | 2006-11-14 | 2012-10-02 | Ams Research Corporation | Anastomosis device and method |
US20080140098A1 (en) * | 2006-11-15 | 2008-06-12 | Monica Kumar | Anastomosis Balloon Configurations and device |
US8491525B2 (en) | 2006-11-17 | 2013-07-23 | Ams Research Corporation | Systems, apparatus and associated methods for needleless delivery of therapeutic fluids |
US8099849B2 (en) | 2006-12-13 | 2012-01-24 | Abbott Cardiovascular Systems Inc. | Optimizing fracture toughness of polymeric stent |
US20080167526A1 (en) * | 2007-01-08 | 2008-07-10 | Crank Justin M | Non-Occlusive, Laterally-Constrained Injection Device |
US20080249608A1 (en) * | 2007-04-04 | 2008-10-09 | Vipul Dave | Bioabsorbable Polymer, Bioabsorbable Composite Stents |
US20080249605A1 (en) | 2007-04-04 | 2008-10-09 | Vipul Dave | Bioabsorbable Polymer, Non-Bioabsorbable Metal Composite Stents |
US8262723B2 (en) | 2007-04-09 | 2012-09-11 | Abbott Cardiovascular Systems Inc. | Implantable medical devices fabricated from polymer blends with star-block copolymers |
US7829008B2 (en) | 2007-05-30 | 2010-11-09 | Abbott Cardiovascular Systems Inc. | Fabricating a stent from a blow molded tube |
US7959857B2 (en) | 2007-06-01 | 2011-06-14 | Abbott Cardiovascular Systems Inc. | Radiation sterilization of medical devices |
US8293260B2 (en) | 2007-06-05 | 2012-10-23 | Abbott Cardiovascular Systems Inc. | Elastomeric copolymer coatings containing poly (tetramethyl carbonate) for implantable medical devices |
US8202528B2 (en) | 2007-06-05 | 2012-06-19 | Abbott Cardiovascular Systems Inc. | Implantable medical devices with elastomeric block copolymer coatings |
US20100070020A1 (en) | 2008-06-11 | 2010-03-18 | Nanovasc, Inc. | Implantable Medical Device |
US8425591B1 (en) | 2007-06-11 | 2013-04-23 | Abbott Cardiovascular Systems Inc. | Methods of forming polymer-bioceramic composite medical devices with bioceramic particles |
US8048441B2 (en) | 2007-06-25 | 2011-11-01 | Abbott Cardiovascular Systems, Inc. | Nanobead releasing medical devices |
US7901452B2 (en) | 2007-06-27 | 2011-03-08 | Abbott Cardiovascular Systems Inc. | Method to fabricate a stent having selected morphology to reduce restenosis |
US7955381B1 (en) | 2007-06-29 | 2011-06-07 | Advanced Cardiovascular Systems, Inc. | Polymer-bioceramic composite implantable medical device with different types of bioceramic particles |
US20090004243A1 (en) | 2007-06-29 | 2009-01-01 | Pacetti Stephen D | Biodegradable triblock copolymers for implantable devices |
US8661630B2 (en) | 2008-05-21 | 2014-03-04 | Abbott Cardiovascular Systems Inc. | Coating comprising an amorphous primer layer and a semi-crystalline reservoir layer |
US7850649B2 (en) | 2007-11-09 | 2010-12-14 | Ams Research Corporation | Mechanical volume control for injection devices |
US9820746B2 (en) | 2008-07-28 | 2017-11-21 | Incube Laboratories LLC | System and method for scaffolding anastomoses |
US20100030139A1 (en) * | 2008-07-30 | 2010-02-04 | Copa Vincent G | Anastomosis Devices and Methods Utilizing Colored Bands |
US8388349B2 (en) * | 2009-01-14 | 2013-03-05 | Ams Research Corporation | Anastomosis deployment force training tool |
US8808353B2 (en) | 2010-01-30 | 2014-08-19 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer scaffolds having a low crossing profile |
US8568471B2 (en) | 2010-01-30 | 2013-10-29 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer scaffolds |
US9173978B2 (en) | 2010-09-22 | 2015-11-03 | Ethicon, Inc. | Bioabsorbable polymeric compositions, processing methods, and medical devices therefrom |
US8747386B2 (en) | 2010-12-16 | 2014-06-10 | Ams Research Corporation | Anastomosis device and related methods |
US8465551B1 (en) * | 2011-07-09 | 2013-06-18 | Bandula Wijay | Temporary prostatic stent for benign prostatic hyperplasia |
US8726483B2 (en) | 2011-07-29 | 2014-05-20 | Abbott Cardiovascular Systems Inc. | Methods for uniform crimping and deployment of a polymer scaffold |
US9381335B2 (en) | 2012-03-21 | 2016-07-05 | Ams Research Corporation | Bladder wall drug delivery system |
US9999527B2 (en) | 2015-02-11 | 2018-06-19 | Abbott Cardiovascular Systems Inc. | Scaffolds having radiopaque markers |
US9700443B2 (en) | 2015-06-12 | 2017-07-11 | Abbott Cardiovascular Systems Inc. | Methods for attaching a radiopaque marker to a scaffold |
Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5357990A (en) * | 1991-08-01 | 1994-10-25 | Gillette Canada Inc. | Flavored dental floss and process |
Family Cites Families (32)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US598051A (en) | 1898-01-25 | Godfried laube | ||
US4889119A (en) | 1985-07-17 | 1989-12-26 | Ethicon, Inc. | Surgical fastener made from glycolide-rich polymer blends |
US4741337A (en) | 1985-07-17 | 1988-05-03 | Ethicon, Inc. | Surgical fastener made from glycolide-rich polymer blends |
US5059211A (en) | 1987-06-25 | 1991-10-22 | Duke University | Absorbable vascular stent |
US5185408A (en) | 1987-12-17 | 1993-02-09 | Allied-Signal Inc. | Medical devices fabricated totally or in part from copolymers of recurring units derived from cyclic carbonates and lactides |
FI85223C (en) | 1988-11-10 | 1992-03-25 | Biocon Oy | BIODEGRADERANDE SURGICAL IMPLANT OCH MEDEL. |
JP3299742B2 (en) * | 1990-05-14 | 2002-07-08 | テルモ株式会社 | Vascular repair material |
US5160341A (en) | 1990-11-08 | 1992-11-03 | Advanced Surgical Intervention, Inc. | Resorbable urethral stent and apparatus for its insertion |
IL102279A (en) | 1991-07-18 | 1996-12-05 | Ethicon Inc | Sterilized bicomponent fiber braids |
US5500013A (en) * | 1991-10-04 | 1996-03-19 | Scimed Life Systems, Inc. | Biodegradable drug delivery vascular stent |
US5443458A (en) | 1992-12-22 | 1995-08-22 | Advanced Cardiovascular Systems, Inc. | Multilayered biodegradable stent and method of manufacture |
US5346501A (en) | 1993-02-05 | 1994-09-13 | Ethicon, Inc. | Laparoscopic absorbable anastomosic fastener and means for applying |
FI942170A (en) | 1993-06-15 | 1994-12-16 | Esa Viherkoski | Tubular device for holding the urethra open |
US5626611A (en) | 1994-02-10 | 1997-05-06 | United States Surgical Corporation | Composite bioabsorbable materials and surgical articles made therefrom |
US5629077A (en) * | 1994-06-27 | 1997-05-13 | Advanced Cardiovascular Systems, Inc. | Biodegradable mesh and film stent |
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 |
US5676685A (en) * | 1995-06-22 | 1997-10-14 | Razavi; Ali | Temporary stent |
US5728135A (en) | 1996-02-09 | 1998-03-17 | Ethicon, Inc. | Stiffened suture for use in a suturing device |
JP3709239B2 (en) | 1996-04-26 | 2005-10-26 | ファナック株式会社 | Magnetic saturation correction method for AC servo motor |
WO1997041916A1 (en) * | 1996-05-03 | 1997-11-13 | Emed Corporation | Combined coronary stent deployment and local delivery of an agent |
US6117168A (en) | 1996-12-31 | 2000-09-12 | Scimed Life Systems, Inc. | Multilayer liquid absorption and deformation devices |
WO1998056312A1 (en) * | 1997-06-13 | 1998-12-17 | Scimed Life Systems, Inc. | Stents having multiple layers of biodegradable polymeric composition |
US5980564A (en) * | 1997-08-01 | 1999-11-09 | Schneider (Usa) Inc. | Bioabsorbable implantable endoprosthesis with reservoir |
JPH11137694A (en) * | 1997-11-13 | 1999-05-25 | Takiron Co Ltd | In-vivo decomposable and absorbable shape memory stent |
US6511748B1 (en) * | 1998-01-06 | 2003-01-28 | Aderans Research Institute, Inc. | Bioabsorbable fibers and reinforced composites produced therefrom |
US6001117A (en) | 1998-03-19 | 1999-12-14 | Indigo Medical, Inc. | Bellows medical construct and apparatus and method for using same |
US6153252A (en) | 1998-06-30 | 2000-11-28 | Ethicon, Inc. | Process for coating stents |
US6120847A (en) | 1999-01-08 | 2000-09-19 | Scimed Life Systems, Inc. | Surface treatment method for stent coating |
US6156373A (en) | 1999-05-03 | 2000-12-05 | Scimed Life Systems, Inc. | Medical device coating methods and devices |
US6258121B1 (en) | 1999-07-02 | 2001-07-10 | Scimed Life Systems, Inc. | Stent coating |
US6338739B1 (en) * | 1999-12-22 | 2002-01-15 | Ethicon, Inc. | Biodegradable stent |
-
1999
- 1999-12-22 US US09/470,620 patent/US6494908B1/en not_active Expired - Lifetime
-
2000
- 2000-12-21 EP EP00311547A patent/EP1112724B1/en not_active Expired - Lifetime
- 2000-12-21 JP JP2000389411A patent/JP4790116B2/en not_active Expired - Fee Related
- 2000-12-21 DE DE60009020T patent/DE60009020T2/en not_active Expired - Lifetime
-
2002
- 2002-07-16 US US10/196,845 patent/US20020177904A1/en not_active Abandoned
Patent Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5357990A (en) * | 1991-08-01 | 1994-10-25 | Gillette Canada Inc. | Flavored dental floss and process |
Cited By (198)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20020002399A1 (en) * | 1999-12-22 | 2002-01-03 | Huxel Shawn Thayer | Removable stent for body lumens |
US6981987B2 (en) | 1999-12-22 | 2006-01-03 | Ethicon, Inc. | Removable stent for body lumens |
US7691078B2 (en) | 2001-05-22 | 2010-04-06 | Boston Scientific Scimed, Inc. | Draining bodily fluids with a stent |
US7918815B2 (en) | 2001-05-22 | 2011-04-05 | Boston Scientific Scimed, Inc. | Draining bodily fluids with a stent |
US6733536B1 (en) * | 2002-10-22 | 2004-05-11 | Scimed Life Systems | Male urethral stent device |
US9387304B2 (en) | 2003-02-21 | 2016-07-12 | C.R. Bard, Inc. | Multi-lumen catheter with separate distal tips |
US8808227B2 (en) | 2003-02-21 | 2014-08-19 | C. R. Bard, Inc. | Multi-lumen catheter with separate distal tips |
US7651529B2 (en) | 2003-05-09 | 2010-01-26 | Boston Scientific Scimed, Inc. | Stricture retractor |
US10806895B2 (en) | 2003-05-27 | 2020-10-20 | Bard Access Systems, Inc. | Methods and apparatus for inserting multi-lumen split-tip catheters into a blood vessel |
US9572956B2 (en) | 2003-05-27 | 2017-02-21 | Bard Access Systems, Inc. | Methods and apparatus for inserting multi-lumen split-tip catheters into a blood vessel |
US8597275B2 (en) | 2003-05-27 | 2013-12-03 | Bard Access Systems, Inc. | Methods and apparatus for inserting multi-lumen split-tip catheters into a blood vessel |
US10105514B2 (en) | 2003-05-27 | 2018-10-23 | Bard Access Systems, Inc. | Methods and apparatus for inserting multi-lumen split-tip catheters into a blood vessel |
US8206371B2 (en) | 2003-05-27 | 2012-06-26 | Bard Access Systems, Inc. | Methods and apparatus for inserting multi-lumen split-tip catheters into a blood vessel |
US7004965B2 (en) * | 2003-12-17 | 2006-02-28 | Yosef Gross | Implant and delivery tool therefor |
US7632297B2 (en) | 2003-12-17 | 2009-12-15 | Prostaplant Ltd. | Implant and delivery tool therefor |
US20060173517A1 (en) * | 2003-12-17 | 2006-08-03 | Yosef Gross | Implant and delivery tool therefor |
US8145321B2 (en) | 2003-12-17 | 2012-03-27 | Yossi Gross | Implant and delivery tool therefor |
US20050137716A1 (en) * | 2003-12-17 | 2005-06-23 | Yosef Gross | Implant and delivery tool therefor |
US9669149B2 (en) | 2004-06-09 | 2017-06-06 | Bard Access Systems, Inc. | Splitable tip catheter with bioresorbable adhesive |
US8992454B2 (en) * | 2004-06-09 | 2015-03-31 | Bard Access Systems, Inc. | Splitable tip catheter with bioresorbable adhesive |
US9782535B2 (en) | 2004-06-09 | 2017-10-10 | Bard Access Systems, Inc. | Splitable tip catheter with bioresorbable adhesive |
WO2006044396A2 (en) | 2004-10-13 | 2006-04-27 | Scimed Life Systems, Inc. | Composite stent with inner and outer stent elements and method of using the same |
US9526613B2 (en) | 2005-03-17 | 2016-12-27 | Valtech Cardio Ltd. | Mitral valve treatment techniques |
US10561498B2 (en) | 2005-03-17 | 2020-02-18 | Valtech Cardio, Ltd. | Mitral valve treatment techniques |
US11497605B2 (en) | 2005-03-17 | 2022-11-15 | Valtech Cardio Ltd. | Mitral valve treatment techniques |
US10695046B2 (en) | 2005-07-05 | 2020-06-30 | Edwards Lifesciences Corporation | Tissue anchor and anchoring system |
US8926695B2 (en) | 2006-12-05 | 2015-01-06 | Valtech Cardio, Ltd. | Segmented ring placement |
US9883943B2 (en) | 2006-12-05 | 2018-02-06 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
US20080262609A1 (en) * | 2006-12-05 | 2008-10-23 | Valtech Cardio, Ltd. | Segmented ring placement |
US10357366B2 (en) | 2006-12-05 | 2019-07-23 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
US10363137B2 (en) | 2006-12-05 | 2019-07-30 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
US11259924B2 (en) | 2006-12-05 | 2022-03-01 | Valtech Cardio Ltd. | Implantation of repair devices in the heart |
US11344414B2 (en) | 2006-12-05 | 2022-05-31 | Valtech Cardio Ltd. | Implantation of repair devices in the heart |
US9974653B2 (en) | 2006-12-05 | 2018-05-22 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
US9872769B2 (en) | 2006-12-05 | 2018-01-23 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
US9351830B2 (en) | 2006-12-05 | 2016-05-31 | Valtech Cardio, Ltd. | Implant and anchor placement |
US11660190B2 (en) | 2007-03-13 | 2023-05-30 | Edwards Lifesciences Corporation | Tissue anchors, systems and methods, and devices |
US20100130815A1 (en) * | 2007-05-18 | 2010-05-27 | Prostaplant Ltd. | Intraurethral and extraurethral apparatus |
US8500939B2 (en) | 2007-10-17 | 2013-08-06 | Bard Access Systems, Inc. | Manufacture of split tip catheters |
US9174019B2 (en) | 2007-10-26 | 2015-11-03 | C. R. Bard, Inc. | Solid-body catheter including lateral distal openings |
US11260161B2 (en) | 2007-10-26 | 2022-03-01 | C. R. Bard, Inc. | Solid-body catheter including lateral distal openings |
US8540661B2 (en) | 2007-10-26 | 2013-09-24 | C. R. Bard, Inc. | Solid-body catheter including lateral distal openings |
US11338075B2 (en) | 2007-10-26 | 2022-05-24 | C. R. Bard, Inc. | Split-tip catheter including lateral distal openings |
US8292841B2 (en) | 2007-10-26 | 2012-10-23 | C. R. Bard, Inc. | Solid-body catheter including lateral distal openings |
US8696614B2 (en) | 2007-10-26 | 2014-04-15 | C. R. Bard, Inc. | Split-tip catheter including lateral distal openings |
US10258732B2 (en) | 2007-10-26 | 2019-04-16 | C. R. Bard, Inc. | Split-tip catheter including lateral distal openings |
US9233200B2 (en) | 2007-10-26 | 2016-01-12 | C.R. Bard, Inc. | Split-tip catheter including lateral distal openings |
US10207043B2 (en) | 2007-10-26 | 2019-02-19 | C. R. Bard, Inc. | Solid-body catheter including lateral distal openings |
US8092415B2 (en) | 2007-11-01 | 2012-01-10 | C. R. Bard, Inc. | Catheter assembly including triple lumen tip |
US10518064B2 (en) | 2007-11-01 | 2019-12-31 | C. R. Bard, Inc. | Catheter assembly including a multi-lumen configuration |
US8894601B2 (en) | 2007-11-01 | 2014-11-25 | C. R. Bard, Inc. | Catheter assembly including triple lumen tip |
US9610422B2 (en) | 2007-11-01 | 2017-04-04 | C. R. Bard, Inc. | Catheter assembly |
US11918758B2 (en) | 2007-11-01 | 2024-03-05 | C. R. Bard, Inc. | Catheter assembly including a multi-lumen configuration |
US9579485B2 (en) | 2007-11-01 | 2017-02-28 | C. R. Bard, Inc. | Catheter assembly including a multi-lumen configuration |
US11660191B2 (en) | 2008-03-10 | 2023-05-30 | Edwards Lifesciences Corporation | Method to reduce mitral regurgitation |
US8926696B2 (en) | 2008-12-22 | 2015-01-06 | Valtech Cardio, Ltd. | Adjustable annuloplasty devices and adjustment mechanisms therefor |
US9636224B2 (en) | 2008-12-22 | 2017-05-02 | Valtech Cardio, Ltd. | Deployment techniques for annuloplasty ring and over-wire rotation tool |
US9277994B2 (en) | 2008-12-22 | 2016-03-08 | Valtech Cardio, Ltd. | Implantation of repair chords in the heart |
US10470882B2 (en) | 2008-12-22 | 2019-11-12 | Valtech Cardio, Ltd. | Closure element for use with annuloplasty structure |
US10517719B2 (en) | 2008-12-22 | 2019-12-31 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
US9011530B2 (en) | 2008-12-22 | 2015-04-21 | Valtech Cardio, Ltd. | Partially-adjustable annuloplasty structure |
US9713530B2 (en) | 2008-12-22 | 2017-07-25 | Valtech Cardio, Ltd. | Adjustable annuloplasty devices and adjustment mechanisms therefor |
US10856986B2 (en) | 2008-12-22 | 2020-12-08 | Valtech Cardio, Ltd. | Adjustable annuloplasty devices and adjustment mechanisms therefor |
US11116634B2 (en) | 2008-12-22 | 2021-09-14 | Valtech Cardio Ltd. | Annuloplasty implants |
US20100161043A1 (en) * | 2008-12-22 | 2010-06-24 | Valtech Cardio, Ltd. | Implantation of repair chords in the heart |
US8808368B2 (en) | 2008-12-22 | 2014-08-19 | Valtech Cardio, Ltd. | Implantation of repair chords in the heart |
US8241351B2 (en) | 2008-12-22 | 2012-08-14 | Valtech Cardio, Ltd. | Adjustable partial annuloplasty ring and mechanism therefor |
US8252050B2 (en) | 2008-12-22 | 2012-08-28 | Valtech Cardio Ltd. | Implantation of repair chords in the heart |
US9662209B2 (en) | 2008-12-22 | 2017-05-30 | Valtech Cardio, Ltd. | Contractible annuloplasty structures |
US10350068B2 (en) | 2009-02-17 | 2019-07-16 | Valtech Cardio, Ltd. | Actively-engageable movement-restriction mechanism for use with an annuloplasty structure |
US8353956B2 (en) | 2009-02-17 | 2013-01-15 | Valtech Cardio, Ltd. | Actively-engageable movement-restriction mechanism for use with an annuloplasty structure |
US11202709B2 (en) | 2009-02-17 | 2021-12-21 | Valtech Cardio Ltd. | Actively-engageable movement-restriction mechanism for use with an annuloplasty structure |
US9561104B2 (en) | 2009-02-17 | 2017-02-07 | Valtech Cardio, Ltd. | Actively-engageable movement-restriction mechanism for use with an annuloplasty structure |
US11076958B2 (en) | 2009-05-04 | 2021-08-03 | Valtech Cardio, Ltd. | Annuloplasty ring delivery catheters |
US9474606B2 (en) | 2009-05-04 | 2016-10-25 | Valtech Cardio, Ltd. | Over-wire implant contraction methods |
US20100280604A1 (en) * | 2009-05-04 | 2010-11-04 | Valtech Cardio, Ltd. | Over-wire rotation tool |
US11844665B2 (en) | 2009-05-04 | 2023-12-19 | Edwards Lifesciences Innovation (Israel) Ltd. | Deployment techniques for annuloplasty structure |
US11185412B2 (en) | 2009-05-04 | 2021-11-30 | Valtech Cardio Ltd. | Deployment techniques for annuloplasty implants |
US11766327B2 (en) | 2009-05-04 | 2023-09-26 | Edwards Lifesciences Innovation (Israel) Ltd. | Implantation of repair chords in the heart |
US8545553B2 (en) | 2009-05-04 | 2013-10-01 | Valtech Cardio, Ltd. | Over-wire rotation tool |
US9968452B2 (en) | 2009-05-04 | 2018-05-15 | Valtech Cardio, Ltd. | Annuloplasty ring delivery cathethers |
US10548729B2 (en) | 2009-05-04 | 2020-02-04 | Valtech Cardio, Ltd. | Deployment techniques for annuloplasty ring and over-wire rotation tool |
US10856987B2 (en) | 2009-05-07 | 2020-12-08 | Valtech Cardio, Ltd. | Multiple anchor delivery tool |
US9937042B2 (en) | 2009-05-07 | 2018-04-10 | Valtech Cardio, Ltd. | Multiple anchor delivery tool |
US8715342B2 (en) | 2009-05-07 | 2014-05-06 | Valtech Cardio, Ltd. | Annuloplasty ring with intra-ring anchoring |
US9119719B2 (en) | 2009-05-07 | 2015-09-01 | Valtech Cardio, Ltd. | Annuloplasty ring with intra-ring anchoring |
US11723774B2 (en) | 2009-05-07 | 2023-08-15 | Edwards Lifesciences Innovation (Israel) Ltd. | Multiple anchor delivery tool |
US9592122B2 (en) | 2009-05-07 | 2017-03-14 | Valtech Cardio, Ltd | Annuloplasty ring with intra-ring anchoring |
US8690939B2 (en) | 2009-10-29 | 2014-04-08 | Valtech Cardio, Ltd. | Method for guide-wire based advancement of a rotation assembly |
US11141271B2 (en) | 2009-10-29 | 2021-10-12 | Valtech Cardio Ltd. | Tissue anchor for annuloplasty device |
US9180007B2 (en) | 2009-10-29 | 2015-11-10 | Valtech Cardio, Ltd. | Apparatus and method for guide-wire based advancement of an adjustable implant |
US9011520B2 (en) | 2009-10-29 | 2015-04-21 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US10098737B2 (en) | 2009-10-29 | 2018-10-16 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US11617652B2 (en) | 2009-10-29 | 2023-04-04 | Edwards Lifesciences Innovation (Israel) Ltd. | Apparatus and method for guide-wire based advancement of an adjustable implant |
US9968454B2 (en) | 2009-10-29 | 2018-05-15 | Valtech Cardio, Ltd. | Techniques for guide-wire based advancement of artificial chordae |
US9414921B2 (en) | 2009-10-29 | 2016-08-16 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US10751184B2 (en) | 2009-10-29 | 2020-08-25 | Valtech Cardio, Ltd. | Apparatus and method for guide-wire based advancement of an adjustable implant |
US8277502B2 (en) | 2009-10-29 | 2012-10-02 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US8940042B2 (en) | 2009-10-29 | 2015-01-27 | Valtech Cardio, Ltd. | Apparatus for guide-wire based advancement of a rotation assembly |
US9622861B2 (en) | 2009-12-02 | 2017-04-18 | Valtech Cardio, Ltd. | Tool for actuating an adjusting mechanism |
US8734467B2 (en) | 2009-12-02 | 2014-05-27 | Valtech Cardio, Ltd. | Delivery tool for implantation of spool assembly coupled to a helical anchor |
US11602434B2 (en) | 2009-12-02 | 2023-03-14 | Edwards Lifesciences Innovation (Israel) Ltd. | Systems and methods for tissue adjustment |
US10492909B2 (en) | 2009-12-02 | 2019-12-03 | Valtech Cardio, Ltd. | Tool for actuating an adjusting mechanism |
US10231831B2 (en) | 2009-12-08 | 2019-03-19 | Cardiovalve Ltd. | Folding ring implant for heart valve |
US10660751B2 (en) | 2009-12-08 | 2020-05-26 | Cardiovalve Ltd. | Prosthetic heart valve with upper skirt |
US11141268B2 (en) | 2009-12-08 | 2021-10-12 | Cardiovalve Ltd. | Prosthetic heart valve with upper and lower skirts |
US11839541B2 (en) | 2009-12-08 | 2023-12-12 | Cardiovalve Ltd. | Prosthetic heart valve with upper skirt |
US10548726B2 (en) | 2009-12-08 | 2020-02-04 | Cardiovalve Ltd. | Rotation-based anchoring of an implant |
US11351026B2 (en) | 2009-12-08 | 2022-06-07 | Cardiovalve Ltd. | Rotation-based anchoring of an implant |
US8475525B2 (en) | 2010-01-22 | 2013-07-02 | 4Tech Inc. | Tricuspid valve repair using tension |
US10433963B2 (en) | 2010-01-22 | 2019-10-08 | 4Tech Inc. | Tissue anchor and delivery tool |
US10405978B2 (en) | 2010-01-22 | 2019-09-10 | 4Tech Inc. | Tricuspid valve repair using tension |
US8961596B2 (en) | 2010-01-22 | 2015-02-24 | 4Tech Inc. | Method and apparatus for tricuspid valve repair using tension |
US10058323B2 (en) | 2010-01-22 | 2018-08-28 | 4 Tech Inc. | Tricuspid valve repair using tension |
US9307980B2 (en) | 2010-01-22 | 2016-04-12 | 4Tech Inc. | Tricuspid valve repair using tension |
US9241702B2 (en) | 2010-01-22 | 2016-01-26 | 4Tech Inc. | Method and apparatus for tricuspid valve repair using tension |
US10238491B2 (en) | 2010-01-22 | 2019-03-26 | 4Tech Inc. | Tricuspid valve repair using tension |
US11653910B2 (en) | 2010-07-21 | 2023-05-23 | Cardiovalve Ltd. | Helical anchor implantation |
US9108017B2 (en) | 2011-03-22 | 2015-08-18 | Applied Medical Resources Corporation | Method of making tubing have drainage holes |
US10792152B2 (en) | 2011-06-23 | 2020-10-06 | Valtech Cardio, Ltd. | Closed band for percutaneous annuloplasty |
US8940044B2 (en) | 2011-06-23 | 2015-01-27 | Valtech Cardio, Ltd. | Closure element for use with an annuloplasty structure |
WO2013006298A3 (en) * | 2011-07-07 | 2013-03-28 | The Regents Of The University Of California | A bioactive spiral coil coating |
US9265608B2 (en) | 2011-11-04 | 2016-02-23 | Valtech Cardio, Ltd. | Implant having multiple rotational assemblies |
US11197759B2 (en) | 2011-11-04 | 2021-12-14 | Valtech Cardio Ltd. | Implant having multiple adjusting mechanisms |
US9775709B2 (en) | 2011-11-04 | 2017-10-03 | Valtech Cardio, Ltd. | Implant having multiple adjustable mechanisms |
US10363136B2 (en) | 2011-11-04 | 2019-07-30 | Valtech Cardio, Ltd. | Implant having multiple adjustment mechanisms |
US8858623B2 (en) | 2011-11-04 | 2014-10-14 | Valtech Cardio, Ltd. | Implant having multiple rotational assemblies |
US9724192B2 (en) | 2011-11-08 | 2017-08-08 | Valtech Cardio, Ltd. | Controlled steering functionality for implant-delivery tool |
US10568738B2 (en) | 2011-11-08 | 2020-02-25 | Valtech Cardio, Ltd. | Controlled steering functionality for implant-delivery tool |
US11857415B2 (en) | 2011-11-08 | 2024-01-02 | Edwards Lifesciences Innovation (Israel) Ltd. | Controlled steering functionality for implant-delivery tool |
US10206673B2 (en) | 2012-05-31 | 2019-02-19 | 4Tech, Inc. | Suture-securing for cardiac valve repair |
US8961594B2 (en) | 2012-05-31 | 2015-02-24 | 4Tech Inc. | Heart valve repair system |
US11395648B2 (en) | 2012-09-29 | 2022-07-26 | Edwards Lifesciences Corporation | Plication lock delivery system and method of use thereof |
US10376266B2 (en) | 2012-10-23 | 2019-08-13 | Valtech Cardio, Ltd. | Percutaneous tissue anchor techniques |
US11344310B2 (en) | 2012-10-23 | 2022-05-31 | Valtech Cardio Ltd. | Percutaneous tissue anchor techniques |
US10893939B2 (en) | 2012-10-23 | 2021-01-19 | Valtech Cardio, Ltd. | Controlled steering functionality for implant delivery tool |
US11890190B2 (en) | 2012-10-23 | 2024-02-06 | Edwards Lifesciences Innovation (Israel) Ltd. | Location indication system for implant-delivery tool |
US9949828B2 (en) | 2012-10-23 | 2018-04-24 | Valtech Cardio, Ltd. | Controlled steering functionality for implant-delivery tool |
US11583400B2 (en) | 2012-12-06 | 2023-02-21 | Edwards Lifesciences Innovation (Israel) Ltd. | Techniques for guided advancement of a tool |
US10610360B2 (en) | 2012-12-06 | 2020-04-07 | Valtech Cardio, Ltd. | Techniques for guide-wire based advancement of a tool |
US9730793B2 (en) | 2012-12-06 | 2017-08-15 | Valtech Cardio, Ltd. | Techniques for guide-wire based advancement of a tool |
US9693865B2 (en) | 2013-01-09 | 2017-07-04 | 4 Tech Inc. | Soft tissue depth-finding tool |
US9788948B2 (en) | 2013-01-09 | 2017-10-17 | 4 Tech Inc. | Soft tissue anchors and implantation techniques |
US10449050B2 (en) | 2013-01-09 | 2019-10-22 | 4 Tech Inc. | Soft tissue depth-finding tool |
US11844691B2 (en) | 2013-01-24 | 2023-12-19 | Cardiovalve Ltd. | Partially-covered prosthetic valves |
USD748252S1 (en) | 2013-02-08 | 2016-01-26 | C. R. Bard, Inc. | Multi-lumen catheter tip |
US11793505B2 (en) | 2013-02-26 | 2023-10-24 | Edwards Lifesciences Corporation | Devices and methods for percutaneous tricuspid valve repair |
US10918374B2 (en) | 2013-02-26 | 2021-02-16 | Edwards Lifesciences Corporation | Devices and methods for percutaneous tricuspid valve repair |
US9907681B2 (en) | 2013-03-14 | 2018-03-06 | 4Tech Inc. | Stent with tether interface |
US11534583B2 (en) | 2013-03-14 | 2022-12-27 | Valtech Cardio Ltd. | Guidewire feeder |
US10449333B2 (en) | 2013-03-14 | 2019-10-22 | Valtech Cardio, Ltd. | Guidewire feeder |
US11890194B2 (en) | 2013-03-15 | 2024-02-06 | Edwards Lifesciences Corporation | Translation catheters, systems, and methods of use thereof |
US10682232B2 (en) | 2013-03-15 | 2020-06-16 | Edwards Lifesciences Corporation | Translation catheters, systems, and methods of use thereof |
US11744573B2 (en) | 2013-08-31 | 2023-09-05 | Edwards Lifesciences Corporation | Devices and methods for locating and implanting tissue anchors at mitral valve commissure |
US10918373B2 (en) | 2013-08-31 | 2021-02-16 | Edwards Lifesciences Corporation | Devices and methods for locating and implanting tissue anchors at mitral valve commissure |
US11766263B2 (en) | 2013-10-23 | 2023-09-26 | Edwards Lifesciences Innovation (Israel) Ltd. | Anchor magazine |
US11065001B2 (en) | 2013-10-23 | 2021-07-20 | Valtech Cardio, Ltd. | Anchor magazine |
US10299793B2 (en) | 2013-10-23 | 2019-05-28 | Valtech Cardio, Ltd. | Anchor magazine |
US10022114B2 (en) | 2013-10-30 | 2018-07-17 | 4Tech Inc. | Percutaneous tether locking |
US10052095B2 (en) | 2013-10-30 | 2018-08-21 | 4Tech Inc. | Multiple anchoring-point tension system |
US10039643B2 (en) | 2013-10-30 | 2018-08-07 | 4Tech Inc. | Multiple anchoring-point tension system |
US10265170B2 (en) | 2013-12-26 | 2019-04-23 | Valtech Cardio, Ltd. | Implantation of flexible implant |
US9610162B2 (en) | 2013-12-26 | 2017-04-04 | Valtech Cardio, Ltd. | Implantation of flexible implant |
US10973637B2 (en) | 2013-12-26 | 2021-04-13 | Valtech Cardio, Ltd. | Implantation of flexible implant |
US9801720B2 (en) | 2014-06-19 | 2017-10-31 | 4Tech Inc. | Cardiac tissue cinching |
US10857330B2 (en) | 2014-07-14 | 2020-12-08 | C. R. Bard, Inc. | Apparatuses, systems, and methods for inserting catheters having enhanced stiffening and guiding features |
US10258768B2 (en) | 2014-07-14 | 2019-04-16 | C. R. Bard, Inc. | Apparatuses, systems, and methods for inserting catheters having enhanced stiffening and guiding features |
US11071628B2 (en) | 2014-10-14 | 2021-07-27 | Valtech Cardio, Ltd. | Leaflet-restraining techniques |
US10195030B2 (en) | 2014-10-14 | 2019-02-05 | Valtech Cardio, Ltd. | Leaflet-restraining techniques |
US11389152B2 (en) | 2014-12-02 | 2022-07-19 | 4Tech Inc. | Off-center tissue anchors with tension members |
US9907547B2 (en) | 2014-12-02 | 2018-03-06 | 4Tech Inc. | Off-center tissue anchors |
US11801135B2 (en) | 2015-02-05 | 2023-10-31 | Cardiovalve Ltd. | Techniques for deployment of a prosthetic valve |
US10925610B2 (en) | 2015-03-05 | 2021-02-23 | Edwards Lifesciences Corporation | Devices for treating paravalvular leakage and methods use thereof |
US10765514B2 (en) | 2015-04-30 | 2020-09-08 | Valtech Cardio, Ltd. | Annuloplasty technologies |
US11020227B2 (en) | 2015-04-30 | 2021-06-01 | Valtech Cardio, Ltd. | Annuloplasty technologies |
US10751182B2 (en) | 2015-12-30 | 2020-08-25 | Edwards Lifesciences Corporation | System and method for reshaping right heart |
US11660192B2 (en) | 2015-12-30 | 2023-05-30 | Edwards Lifesciences Corporation | System and method for reshaping heart |
US10828160B2 (en) | 2015-12-30 | 2020-11-10 | Edwards Lifesciences Corporation | System and method for reducing tricuspid regurgitation |
US11890193B2 (en) | 2015-12-30 | 2024-02-06 | Edwards Lifesciences Corporation | System and method for reducing tricuspid regurgitation |
US11937795B2 (en) | 2016-02-16 | 2024-03-26 | Cardiovalve Ltd. | Techniques for providing a replacement valve and transseptal communication |
US11540835B2 (en) | 2016-05-26 | 2023-01-03 | Edwards Lifesciences Corporation | Method and system for closing left atrial appendage |
US10702274B2 (en) | 2016-05-26 | 2020-07-07 | Edwards Lifesciences Corporation | Method and system for closing left atrial appendage |
US10226342B2 (en) | 2016-07-08 | 2019-03-12 | Valtech Cardio, Ltd. | Adjustable annuloplasty device with alternating peaks and troughs |
US10959845B2 (en) | 2016-07-08 | 2021-03-30 | Valtech Cardio, Ltd. | Adjustable annuloplasty device with alternating peaks and troughs |
US11779458B2 (en) | 2016-08-10 | 2023-10-10 | Cardiovalve Ltd. | Prosthetic valve with leaflet connectors |
US11883611B2 (en) | 2017-04-18 | 2024-01-30 | Edwards Lifesciences Corporation | Catheter system with linear actuation control mechanism |
US11045627B2 (en) | 2017-04-18 | 2021-06-29 | Edwards Lifesciences Corporation | Catheter system with linear actuation control mechanism |
US10806579B2 (en) | 2017-10-20 | 2020-10-20 | Boston Scientific Scimed, Inc. | Heart valve repair implant for treating tricuspid regurgitation |
US10835221B2 (en) | 2017-11-02 | 2020-11-17 | Valtech Cardio, Ltd. | Implant-cinching devices and systems |
US11832784B2 (en) | 2017-11-02 | 2023-12-05 | Edwards Lifesciences Innovation (Israel) Ltd. | Implant-cinching devices and systems |
US11135062B2 (en) | 2017-11-20 | 2021-10-05 | Valtech Cardio Ltd. | Cinching of dilated heart muscle |
US11779463B2 (en) | 2018-01-24 | 2023-10-10 | Edwards Lifesciences Innovation (Israel) Ltd. | Contraction of an annuloplasty structure |
US11666442B2 (en) | 2018-01-26 | 2023-06-06 | Edwards Lifesciences Innovation (Israel) Ltd. | Techniques for facilitating heart valve tethering and chord replacement |
US11890191B2 (en) | 2018-07-12 | 2024-02-06 | Edwards Lifesciences Innovation (Israel) Ltd. | Fastener and techniques therefor |
US11123191B2 (en) | 2018-07-12 | 2021-09-21 | Valtech Cardio Ltd. | Annuloplasty systems and locking tools therefor |
US11819411B2 (en) | 2019-10-29 | 2023-11-21 | Edwards Lifesciences Innovation (Israel) Ltd. | Annuloplasty and tissue anchor technologies |
US11857417B2 (en) | 2020-08-16 | 2024-01-02 | Trilio Medical Ltd. | Leaflet support |
US11969348B2 (en) | 2021-08-26 | 2024-04-30 | Edwards Lifesciences Corporation | Cardiac valve replacement |
Also Published As
Publication number | Publication date |
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EP1112724A2 (en) | 2001-07-04 |
JP4790116B2 (en) | 2011-10-12 |
US6494908B1 (en) | 2002-12-17 |
EP1112724A3 (en) | 2002-06-12 |
EP1112724B1 (en) | 2004-03-17 |
JP2001299932A (en) | 2001-10-30 |
DE60009020T2 (en) | 2005-03-10 |
DE60009020D1 (en) | 2004-04-22 |
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