CA2563023A1 - Polymer-based stent assembly - Google Patents
Polymer-based stent assembly Download PDFInfo
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- CA2563023A1 CA2563023A1 CA002563023A CA2563023A CA2563023A1 CA 2563023 A1 CA2563023 A1 CA 2563023A1 CA 002563023 A CA002563023 A CA 002563023A CA 2563023 A CA2563023 A CA 2563023A CA 2563023 A1 CA2563023 A1 CA 2563023A1
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- cylindrical device
- polymeric
- stent
- diameter
- polymer
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Classifications
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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
-
- 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
-
- 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
- A61L31/04—Macromolecular materials
- A61L31/06—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
- C08L67/00—Compositions of polyesters obtained by reactions forming a carboxylic ester link in the main chain; Compositions of derivatives of such polymers
- C08L67/04—Polyesters derived from hydroxycarboxylic acids, e.g. lactones
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/9522—Means for mounting a stent or stent-graft onto or into a placement instrument
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/958—Inflatable balloons for placing stents or stent-grafts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- 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
Abstract
Methods for preparing a polymer-based stmt assembly comprising an inflatable balloon catheter and a polymer-based stmt resistant to relaxation-related negative recoil are provided. The methods comprise heating a polymeric cylindrical device which is at a final predetermined shape and diameter to a temperature sufficiently above the glass transition temperature (Tg) of the polymer and for a time sufficient to erase any memory of previous processing of the polymeric cylindrical device and then quenching the polymeric cylindrical device to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter and shape, mounting the educated cylindrical device on an inflatable balloon catheter, reducing the diameter of the educated cylindrical device by heating to a temperature at or slightly above the Tg of the polymer while evenly applying pressure on the exterior surface of the wall of the cylindrical device, and then cooling the cylindrical device below the Tg of the polymer to provide a stmt assembly comprising an inflatable balloon catheter and an expandable, educated, polymeric stmt snugly and stably disposed thereon. Assemblies comprising an inflatable balloon and a polymer based stmt that is substantially resistant to relaxation related recoil mounted snugly on the balloon are also provided.
Claims (26)
1. A method for preparing an assembly for delivering a degradable and bioresorbable polymeric stent that is resistant to relaxation-related recoil to a mammalian subject, comprising:
(a) heating a polymeric cylindrical device which is at a final predetermined radial diameter and wall thickness to a temperature sufficiently above the glass transition temperature (Tg) of the polymer and for a time sufficient to erase memory of previous processing of the polymeric device, wherein the polymeric cylindrical device has a wall defining a first open end, a second open end, and a channel connecting the first and the second open end;
(b) rapidly cooling the polymeric cylindrical device at a temperature below the Tg of the polymer to quench the polymeric cylindrical device and to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter and shape;
(c) forming slits, voids, or open spaces in the wall of the polymeric cylindrical device prior to step (a) or after step (b), wherein the slits, voids, or open spaces are configured to allow a reduction in diameter of the device without substantially altering the wall thickness of the device;
(d) mounting the educated polymeric cylindrical device on an inflatable balloon catheter;
(e) reducing the diameter of the cylindrical device by heating the cylindrical device to a temperature at or slightly above the Tg of the polymer while evenly applying pressure on the exterior surface of the wall of the cylindrical device; and (f) then rapidly cooling the cylindrical device below the Tg of the polymer to provide an assembly comprising a inflatable balloon catheter and an expandable polymeric stent which is substantially resistant to relaxation-related recoil when implanted in the lumen of a tube, duct, or vessel of the mammalian subject or when expanded and stored at 37° C for 4 to 6 weeks.
(a) heating a polymeric cylindrical device which is at a final predetermined radial diameter and wall thickness to a temperature sufficiently above the glass transition temperature (Tg) of the polymer and for a time sufficient to erase memory of previous processing of the polymeric device, wherein the polymeric cylindrical device has a wall defining a first open end, a second open end, and a channel connecting the first and the second open end;
(b) rapidly cooling the polymeric cylindrical device at a temperature below the Tg of the polymer to quench the polymeric cylindrical device and to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter and shape;
(c) forming slits, voids, or open spaces in the wall of the polymeric cylindrical device prior to step (a) or after step (b), wherein the slits, voids, or open spaces are configured to allow a reduction in diameter of the device without substantially altering the wall thickness of the device;
(d) mounting the educated polymeric cylindrical device on an inflatable balloon catheter;
(e) reducing the diameter of the cylindrical device by heating the cylindrical device to a temperature at or slightly above the Tg of the polymer while evenly applying pressure on the exterior surface of the wall of the cylindrical device; and (f) then rapidly cooling the cylindrical device below the Tg of the polymer to provide an assembly comprising a inflatable balloon catheter and an expandable polymeric stent which is substantially resistant to relaxation-related recoil when implanted in the lumen of a tube, duct, or vessel of the mammalian subject or when expanded and stored at 37° C for 4 to 6 weeks.
2. The method of claim 1 wherein the cylindrical device is mounted on a support for maintaining the diameter and shape of the device during step (a) and step (b).
3. The method of claim 1 wherein the stent is formed from a polymer selected from PLA
and stereocopolymers (copolymers composed of L and D units), PLAGA, Poly(lactic-co-glycolic-co-gluconic acid.
and stereocopolymers (copolymers composed of L and D units), PLAGA, Poly(lactic-co-glycolic-co-gluconic acid.
4. The method of claim 1 wherein the cylindrical device is reduced to a diameter that is less than the diameter of the lumen of the target duct, tube, or vessel during step (e).
5. The method of claim 1 wherein the wall thickness of the cylindrical device is substantially the same before and after step (e).
6. A method for preparing an assembly for delivering a degradable and bioresorbable polymeric stent into the lumen of a tube, duct, or vessel of a mammalian subject, comprising:
(a) providing a polymeric cylindrical device comprising a wall defining a first open end, a second open end, and a channel connecting said first open end and said second open end, wherein the cylindrical device has a diameter and wall thickness comparable to the final desired diameter and wall thickness of the stent;
(b) educating the device by erasing memory of previous processing of the polymeric device and establishing a memory of the desired diameter; wherein such education is achieved by heating the device to a temperature at least 8 degrees C above the Tg of the polymer;
(c) quenching the device to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter and shape;
(d) forming slits, voids, or open spaces in the wall of the polymeric cylindrical device before or after the device is educated;
(e) mounting the educated polymeric cylindrical device on an inflatable balloon catheter;
(f) crimping the cylindrical device on the inflatable balloon catheter while heating the cylindrical device to a temperature at or slightly above the Tg of the polymer; and (g) then rapidly cooling the cylindrical device below the Tg of the polymer to provide an assembly comprising an inflatable balloon catheter and an expandable polymeric stent which is substantially resistant to relaxation-related recoil when implanted in the lumen of a tube, duct, or vessel of a mammalian subject or when expanded to a final predetermined shape and diameter and stored at 37°C for 4 weeks or more.
(a) providing a polymeric cylindrical device comprising a wall defining a first open end, a second open end, and a channel connecting said first open end and said second open end, wherein the cylindrical device has a diameter and wall thickness comparable to the final desired diameter and wall thickness of the stent;
(b) educating the device by erasing memory of previous processing of the polymeric device and establishing a memory of the desired diameter; wherein such education is achieved by heating the device to a temperature at least 8 degrees C above the Tg of the polymer;
(c) quenching the device to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter and shape;
(d) forming slits, voids, or open spaces in the wall of the polymeric cylindrical device before or after the device is educated;
(e) mounting the educated polymeric cylindrical device on an inflatable balloon catheter;
(f) crimping the cylindrical device on the inflatable balloon catheter while heating the cylindrical device to a temperature at or slightly above the Tg of the polymer; and (g) then rapidly cooling the cylindrical device below the Tg of the polymer to provide an assembly comprising an inflatable balloon catheter and an expandable polymeric stent which is substantially resistant to relaxation-related recoil when implanted in the lumen of a tube, duct, or vessel of a mammalian subject or when expanded to a final predetermined shape and diameter and stored at 37°C for 4 weeks or more.
7. A method for preparing an assembly for delivering a degradable and bioresorbable polymeric stent into the lumen of a tube, duct, or vessel of a mammalian subject, comprising:
(a) providing a hollow, cylindrical device comprising a wall having slits, openings, or voids therein, wherein the hollow cylindrical device has a radial diameter that is less than the final predetermined diameter of the stent;
(b) heating the polymeric cylindrical device to a temperature close to or above the Tg of the polymer while expanding the tube to the final predetermined diameter;
(c) mounting the cylindrical device on a support for maintaining the cylindrical device at the final predetermined diameter;
(d) heating the mounted cylindrical device to a temperature sufficiently above the glass transition temperature (Tg) of the polymer and for a time sufficient to erase memory of previous processing of the polymeric device;
(e) rapidly cooling the polymeric cylindrical device at a temperature below the Tg of the polymer to quench the polymeric cylindrical device and to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter;
(f) mounting the educated polymeric cylindrical device on an inflatable balloon catheter;
(g) reducing the diameter of the cylindrical device by heating the cylindrical device to a temperature at or slightly above the Tg of the polymer while evenly applying pressure on the exterior surface of the wall of the cylindrical device; and (h) then rapidly cooling the cylindrical device below the Tg of the polymer to provide an assembly comprising a inflatable balloon catheter and an expandable polymeric stent which is substantially resistant to relaxation-related recoil when implanted in the lumen of a tube, duct, or vessel of a mammalian subject or when expanded to a final predetermined shape and diameter and stored at 37°C for 4 weeks or more.
(a) providing a hollow, cylindrical device comprising a wall having slits, openings, or voids therein, wherein the hollow cylindrical device has a radial diameter that is less than the final predetermined diameter of the stent;
(b) heating the polymeric cylindrical device to a temperature close to or above the Tg of the polymer while expanding the tube to the final predetermined diameter;
(c) mounting the cylindrical device on a support for maintaining the cylindrical device at the final predetermined diameter;
(d) heating the mounted cylindrical device to a temperature sufficiently above the glass transition temperature (Tg) of the polymer and for a time sufficient to erase memory of previous processing of the polymeric device;
(e) rapidly cooling the polymeric cylindrical device at a temperature below the Tg of the polymer to quench the polymeric cylindrical device and to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter;
(f) mounting the educated polymeric cylindrical device on an inflatable balloon catheter;
(g) reducing the diameter of the cylindrical device by heating the cylindrical device to a temperature at or slightly above the Tg of the polymer while evenly applying pressure on the exterior surface of the wall of the cylindrical device; and (h) then rapidly cooling the cylindrical device below the Tg of the polymer to provide an assembly comprising a inflatable balloon catheter and an expandable polymeric stent which is substantially resistant to relaxation-related recoil when implanted in the lumen of a tube, duct, or vessel of a mammalian subject or when expanded to a final predetermined shape and diameter and stored at 37°C for 4 weeks or more.
8. The method of claim 6 wherein the stent is formed from a polymer selected from PLA
and stereocopolymers (copolymers composed of L and D units), PLAGA, Poly(lactic-co-glycolic-co-gluconic acid.
and stereocopolymers (copolymers composed of L and D units), PLAGA, Poly(lactic-co-glycolic-co-gluconic acid.
9. The method of claim 6 wherein the wall thickness of the cylindrical device is substantially the same before and after step (g).
10. A method for preparing an assembly for delivering a degradable and bioresorbable polymeric stent into the lumen of a tube, duct, or vessel of a mammalian subject, comprising:
(a) providing a polymeric cylindrical device comprising a wall defining a first open end, a second open end, and a channel connecting said first open end and said second open end, and having slits, voids, or open spaces for permitting expansion and contraction of the device without substantially altering the thickness of the wall, wherein the cylindrical device has a radial diameter that is less than the final desired diameter of the stent, (b) expanding the polymeric device to the final desired diameter while heating to a temperature close to or above the Tg of the polymer;
(c) educating the device by erasing memory of previous processing of the polymeric device and establishing a memory of the desired diameter; wherein such education is achieved by heating the device, which is mounted on a support, to a temperature at least 8 degrees C above the Tg of the polymer;
(c) quenching the device to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter and shape;
(d) mounting the educated polymeric cylindrical device on an inflatable balloon catheter;
(e) crimping the cylindrical device on the inflatable balloon catheter while heating the cylindrical device to a temperature at or slightly above the Tg of the polymer; and (f) then rapidly cooling the cylindrical device below the Tg of the polymer to provide an assembly comprising a inflatable balloon catheter and an expandable polymeric stent which is substantially resistant to relaxation-related recoil when implanted in the lumen of a tube, duct, or vessel of a mammalian subject or when expanded to a final predetermined shape and diameter and stored at 37°C for 4 weeks or more.
(a) providing a polymeric cylindrical device comprising a wall defining a first open end, a second open end, and a channel connecting said first open end and said second open end, and having slits, voids, or open spaces for permitting expansion and contraction of the device without substantially altering the thickness of the wall, wherein the cylindrical device has a radial diameter that is less than the final desired diameter of the stent, (b) expanding the polymeric device to the final desired diameter while heating to a temperature close to or above the Tg of the polymer;
(c) educating the device by erasing memory of previous processing of the polymeric device and establishing a memory of the desired diameter; wherein such education is achieved by heating the device, which is mounted on a support, to a temperature at least 8 degrees C above the Tg of the polymer;
(c) quenching the device to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter and shape;
(d) mounting the educated polymeric cylindrical device on an inflatable balloon catheter;
(e) crimping the cylindrical device on the inflatable balloon catheter while heating the cylindrical device to a temperature at or slightly above the Tg of the polymer; and (f) then rapidly cooling the cylindrical device below the Tg of the polymer to provide an assembly comprising a inflatable balloon catheter and an expandable polymeric stent which is substantially resistant to relaxation-related recoil when implanted in the lumen of a tube, duct, or vessel of a mammalian subject or when expanded to a final predetermined shape and diameter and stored at 37°C for 4 weeks or more.
11. An assembly comprising an inflatable balloon and a polymeric stent prepared in accordance with the method of claim 1, 6, 7, or 10.
12. An assembly for introducing a degradable and bioresorbable stent into a vessel, tube, or duct of a mammalian subject, comprising:
an inflatable balloon catheter, and a stent formed from a degradable polymeric material having a Tg at least 45°
mounted thereon, wherein the stent comprises a wall defining a first open end, a second open end, and a channel connecting the first and second open end, and wherein the wall of stent includes voids, open spaces, or slits that allow the stent to be expanded to a larger diameter, a shorter length, and the same wall thickness when the balloon catheter is inflated or when the stent is heated to a temperature above the Tg of the polymer, and wherein the stent exhibits little to no negative recoil when deployed in the blood vessel of a subject or when expanded to a final predetermined shape and diameter and stored at 37°C for 4 weeks or more; and wherein the assembly has a diameter that allows it to be inserted into a tube, vessel or duct of the subject and advanced to a target site.
an inflatable balloon catheter, and a stent formed from a degradable polymeric material having a Tg at least 45°
mounted thereon, wherein the stent comprises a wall defining a first open end, a second open end, and a channel connecting the first and second open end, and wherein the wall of stent includes voids, open spaces, or slits that allow the stent to be expanded to a larger diameter, a shorter length, and the same wall thickness when the balloon catheter is inflated or when the stent is heated to a temperature above the Tg of the polymer, and wherein the stent exhibits little to no negative recoil when deployed in the blood vessel of a subject or when expanded to a final predetermined shape and diameter and stored at 37°C for 4 weeks or more; and wherein the assembly has a diameter that allows it to be inserted into a tube, vessel or duct of the subject and advanced to a target site.
13. The assembly of claim 12, wherein the assembly has a diameter that allows the stent to be inserted into a blood vessel of a human subject and advanced to stenotic lesion.
14. The assembly of claim 12 wherein the stent exhibits positive recoil and adaptation to the geometry of the artery when the stent is not fully deployed up to its final diameter during deployment.
15. The assembly of claim 12 wherein the stent is formed from a polymer selected from PLA and stereocopolymers (copolymers composed of L and D units), PLAGA, Poly(lactic-co-glycolic-co-gluconic acid.
16. The assembly of claim 12 wherein the stent is stably mounted on the balloon.
17. The assembly of claim 12 further comprising a retractable sheath covering the exterior surface of the stent.
18. The assembly of claim 12 wherein bioactive agent or tracking agent is disposed within or on a surface of the stent.
19. A method for preparing a degradable and bioresorbable polymeric stent for implantation into the lumen of a tube, duct, or vessel of a mammalian subject, comprising:
(a) heating a polymeric cylindrical device which is at a final predetermined radial diameter and wall thickness to a temperature sufficiently above the glass transition temperature (Tg) of the polymer and for a time sufficient to erase memory of previous processing of the polymeric device, wherein the polymeric cylindrical device has a wall defining a first open end, a second open end, and a channel connecting the first and the second open end;
(b) rapidly cooling the polymeric cylindrical device at a temperature below the Tg of the polymer to quench the polymeric cylindrical device and to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter and shape;
and (c) forming slits, voids, or open spaces in the wall of the polymeric cylindrical device prior to step (a) or after step (b), wherein the stent is resistant to relaxation-related recoil when deployed in the blood vessel of a subject or when expanded to a final predetermined shape and diameter and stored at 37°C for 4 weeks or more.
(a) heating a polymeric cylindrical device which is at a final predetermined radial diameter and wall thickness to a temperature sufficiently above the glass transition temperature (Tg) of the polymer and for a time sufficient to erase memory of previous processing of the polymeric device, wherein the polymeric cylindrical device has a wall defining a first open end, a second open end, and a channel connecting the first and the second open end;
(b) rapidly cooling the polymeric cylindrical device at a temperature below the Tg of the polymer to quench the polymeric cylindrical device and to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter and shape;
and (c) forming slits, voids, or open spaces in the wall of the polymeric cylindrical device prior to step (a) or after step (b), wherein the stent is resistant to relaxation-related recoil when deployed in the blood vessel of a subject or when expanded to a final predetermined shape and diameter and stored at 37°C for 4 weeks or more.
20. The method of claim 19 wherein the cylindrical device is mounted on a support for maintaining the diameter and shape of the device during step (a) and step (b) .
21. The method of claim 19 wherein the stent is formed from a polymer selected from PLA and stereocopolymers (copolymers composed of L and D units), PLAGA, Poly(lactic-co-glycolic-co-gluconic acid.
22 22. A method for preparing a degradable and bioresorbable polymeric stent that is resistant to relaxation-related recoil when implanted into the lumen of a tube, duct, or vessel of a mammalian subject or when expanded to a final predetermined shape and diameter and stored at 37°C for 4 weeks or more, comprising:
(a) providing a hollow, cylindrical device comprising a wall having slits, openings, or voids therein, wherein the hollow cylindrical device has a radial diameter that is less than the final predetermined diameter of the stent;
(b) heating the polymeric cylindrical device to a temperature close to or above the Tg of the polymer while expanding the tube to the final predetermined diameter;
(c) mounting the cylindrical device on a support for maintaining the cylindrical device at the final predetermined diameter;
(d) heating the mounted cylindrical device to a temperature sufficiently above the glass transition temperature (Tg) of the polymer and for a time sufficient to erase memory of previous processing of the polymeric device; and (e) rapidly cooling the polymeric cylindrical device at a temperature below the Tg of the polymer to quench the polymeric cylindrical device and to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter.
(a) providing a hollow, cylindrical device comprising a wall having slits, openings, or voids therein, wherein the hollow cylindrical device has a radial diameter that is less than the final predetermined diameter of the stent;
(b) heating the polymeric cylindrical device to a temperature close to or above the Tg of the polymer while expanding the tube to the final predetermined diameter;
(c) mounting the cylindrical device on a support for maintaining the cylindrical device at the final predetermined diameter;
(d) heating the mounted cylindrical device to a temperature sufficiently above the glass transition temperature (Tg) of the polymer and for a time sufficient to erase memory of previous processing of the polymeric device; and (e) rapidly cooling the polymeric cylindrical device at a temperature below the Tg of the polymer to quench the polymeric cylindrical device and to provide an educated polymeric cylindrical device having a memory of the final predetermined diameter.
23. The method of claim 22 wherein the stent is formed from a polymer selected from PLA and stereocopolymers (copolymers composed of L and D units), PLAGA, Poly(lactic-co-glycolic-co-gluconic acid.
24. A stent made in accordance with the methods of claims 19 or 22.
25. A stent substantially resistant to relaxation-related recoil when implanted in the lumen of a duct, vessel, or tube of a mammalian subject recoil or when expanded to a final predetermined shape and diameter and stored at 37°C for 4 weeks or more, wherein said stent is formed from a polymer has a Tg of 45°C or greater, and wherein said stent lacks a memory of processing, and has a memory of a final predetermined shape and diameter.
26. A method of reducing the risk of chronic restenosis that can occur in an artery of a patient following PTC angioplasty, comprising:
delivering the assembly of claim 12 to the locus of a stenotic lesion;
inflating the balloon to expand the stent to a diameter equal to or less than the final predetermined diameter; and deflating and withdrawing the balloon.
delivering the assembly of claim 12 to the locus of a stenotic lesion;
inflating the balloon to expand the stent to a diameter equal to or less than the final predetermined diameter; and deflating and withdrawing the balloon.
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
PCT/EP2004/004133 WO2005096992A1 (en) | 2004-04-02 | 2004-04-02 | Polymer-based stent assembly |
Publications (2)
Publication Number | Publication Date |
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CA2563023A1 true CA2563023A1 (en) | 2005-10-20 |
CA2563023C CA2563023C (en) | 2012-01-24 |
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Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
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CA2563023A Expired - Fee Related CA2563023C (en) | 2004-04-02 | 2004-04-02 | Polymer-based stent assembly |
Country Status (13)
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US (2) | US7731740B2 (en) |
EP (1) | EP1737387B1 (en) |
JP (1) | JP4665109B2 (en) |
KR (1) | KR101098267B1 (en) |
CN (1) | CN1960684B (en) |
AT (1) | ATE442822T1 (en) |
AU (1) | AU2004318159B8 (en) |
BR (1) | BRPI0418712B8 (en) |
CA (1) | CA2563023C (en) |
DE (1) | DE602004023237D1 (en) |
ES (1) | ES2330849T3 (en) |
HK (1) | HK1102420A1 (en) |
WO (1) | WO2005096992A1 (en) |
Families Citing this family (71)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
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 |
CN100558321C (en) * | 2003-06-16 | 2009-11-11 | 南洋理工大学 | Polymer Scaffold And Its Manufacturing Methods |
ATE442822T1 (en) * | 2004-04-02 | 2009-10-15 | Arterial Remodelling Technolog | POLYMER-BASED STENT ARRANGEMENT |
US20060013853A1 (en) * | 2004-07-19 | 2006-01-19 | Richard Robert E | Medical devices having conductive substrate and covalently bonded coating layer |
US7971333B2 (en) | 2006-05-30 | 2011-07-05 | Advanced Cardiovascular Systems, Inc. | Manufacturing process for polymetric stents |
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 |
US7731890B2 (en) | 2006-06-15 | 2010-06-08 | Advanced Cardiovascular Systems, Inc. | Methods of fabricating stents with enhanced fracture toughness |
US20140107761A1 (en) | 2004-07-26 | 2014-04-17 | Abbott Cardiovascular Systems Inc. | Biodegradable stent with enhanced fracture toughness |
US20070010736A1 (en) * | 2005-05-19 | 2007-01-11 | Biophan Technologies, Inc. | Electromagnetic resonant circuit sleeve for implantable medical device |
US20070038290A1 (en) * | 2005-08-15 | 2007-02-15 | Bin Huang | Fiber reinforced composite stents |
US20090076594A1 (en) * | 2006-03-14 | 2009-03-19 | Patrick Sabaria | Method of monitoring positioning of polymer stents |
EP2020956A2 (en) | 2006-05-26 | 2009-02-11 | Nanyang Technological University | Implantable article, method of forming same and method for reducing thrombogenicity |
US8333000B2 (en) * | 2006-06-19 | 2012-12-18 | Advanced Cardiovascular Systems, Inc. | Methods for improving stent retention on a balloon catheter |
US8460364B2 (en) | 2006-07-20 | 2013-06-11 | Orbusneich Medical, Inc. | Bioabsorbable polymeric medical device |
WO2008011612A2 (en) | 2006-07-20 | 2008-01-24 | Orbusneich Medical, Inc. | Bioabsorbable polymeric medical device |
EP3009477B1 (en) | 2006-07-20 | 2024-01-24 | Orbusneich Medical Pte. Ltd | Bioabsorbable polymeric composition for a medical device |
US7959942B2 (en) | 2006-10-20 | 2011-06-14 | Orbusneich Medical, Inc. | Bioabsorbable medical device with coating |
EP2073754A4 (en) | 2006-10-20 | 2012-09-26 | Orbusneich Medical Inc | Bioabsorbable polymeric composition and medical device background |
WO2008084286A2 (en) * | 2006-10-25 | 2008-07-17 | Arterial Remodeling Technologies, S.A. | Method for expansion and deployment of polymeric structures including stents |
US20130150943A1 (en) | 2007-01-19 | 2013-06-13 | Elixir Medical Corporation | Biodegradable endoprostheses and methods for their fabrication |
US20080177373A1 (en) * | 2007-01-19 | 2008-07-24 | Elixir Medical Corporation | Endoprosthesis structures having supporting features |
US8814930B2 (en) | 2007-01-19 | 2014-08-26 | Elixir Medical Corporation | Biodegradable endoprosthesis and methods for their fabrication |
US8002817B2 (en) * | 2007-05-04 | 2011-08-23 | Abbott Cardiovascular Systems Inc. | Stents with high radial strength and methods of manufacturing same |
US20090163985A1 (en) * | 2007-12-19 | 2009-06-25 | Vipul Dave | Method of Retaining a Polymeric Stent on an Expansion Member |
US8414638B2 (en) * | 2008-03-12 | 2013-04-09 | Abbott Cardiovascular Systems Inc. | Method for fabricating a polymer stent with break-away links for enhanced stent retenton |
US10898620B2 (en) | 2008-06-20 | 2021-01-26 | Razmodics Llc | Composite stent having multi-axial flexibility and method of manufacture thereof |
US8206635B2 (en) | 2008-06-20 | 2012-06-26 | Amaranth Medical Pte. | Stent fabrication via tubular casting processes |
US8206636B2 (en) | 2008-06-20 | 2012-06-26 | Amaranth Medical Pte. | Stent fabrication via tubular casting processes |
US8992601B2 (en) | 2009-05-20 | 2015-03-31 | 480 Biomedical, Inc. | Medical implants |
EP2432425B1 (en) | 2009-05-20 | 2018-08-08 | 480 Biomedical, Inc. | Medical implant |
US9309347B2 (en) | 2009-05-20 | 2016-04-12 | Biomedical, Inc. | Bioresorbable thermoset polyester/urethane elastomers |
US9265633B2 (en) | 2009-05-20 | 2016-02-23 | 480 Biomedical, Inc. | Drug-eluting medical implants |
US8888840B2 (en) * | 2009-05-20 | 2014-11-18 | Boston Scientific Scimed, Inc. | Drug eluting medical implant |
US20110319987A1 (en) | 2009-05-20 | 2011-12-29 | Arsenal Medical | Medical implant |
BR112012007955B1 (en) | 2009-10-06 | 2020-07-21 | Sahajanand Medical Technologies Private Limited | bioresorbable vascular implant |
US8808353B2 (en) | 2010-01-30 | 2014-08-19 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer scaffolds having a low crossing profile |
SI2752172T1 (en) * | 2010-01-30 | 2016-10-28 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer stents |
US8568471B2 (en) | 2010-01-30 | 2013-10-29 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer scaffolds |
US8261423B2 (en) | 2010-04-30 | 2012-09-11 | Abbott Cardiovascular Systems Inc. | Methods for crimping a polymeric stent onto a delivery balloon |
US8844113B2 (en) * | 2010-04-30 | 2014-09-30 | Abbott Cardiovascular Systems, Inc. | Methods for crimping a polymeric stent scaffold onto a delivery balloon |
US9345602B2 (en) * | 2010-09-23 | 2016-05-24 | Abbott Cardiovascular Systems Inc. | Processes for making crush recoverable polymer scaffolds |
CN102429749A (en) * | 2011-07-27 | 2012-05-02 | 微创医疗器械(上海)有限公司 | Novel processing method for biodegradable stent |
US8726483B2 (en) | 2011-07-29 | 2014-05-20 | Abbott Cardiovascular Systems Inc. | Methods for uniform crimping and deployment of a polymer scaffold |
CN102379762B (en) * | 2011-08-02 | 2015-03-25 | 上海微创医疗器械(集团)有限公司 | Biodegradable stent with groove and preparation method thereof |
CN102247623B (en) * | 2011-08-17 | 2014-07-23 | 上海微创医疗器械(集团)有限公司 | Multilayer degradable stent having shape memory and preparation method thereof |
CN102327652A (en) * | 2011-09-28 | 2012-01-25 | 微创医疗器械(上海)有限公司 | Biodegradable stent and preparation method thereof |
US8968387B2 (en) | 2012-07-23 | 2015-03-03 | Abbott Cardiovascular Systems Inc. | Shape memory bioresorbable polymer peripheral scaffolds |
JP6267214B2 (en) * | 2012-10-25 | 2018-01-24 | アルテリアル・ルモンドラン・テクノロジー・エス・アー | Method for crimping a bioresorbable stent |
EP2916901B1 (en) | 2012-11-12 | 2020-06-24 | Hollister Incorporated | Intermittent catheter assembly |
WO2014077886A1 (en) | 2012-11-14 | 2014-05-22 | Hollister Incorporated | Disposable catheter with selectively degradable inner core |
WO2014188437A2 (en) | 2013-05-23 | 2014-11-27 | S.T.S. Medical Ltd. | Shape change structure |
EP3862031B1 (en) | 2013-11-08 | 2023-08-09 | Hollister Incorporated | Oleophilic lubricated catheters |
US10420859B2 (en) | 2013-12-12 | 2019-09-24 | Hollister Incorporated | Flushable catheters |
EP3079752B1 (en) | 2013-12-12 | 2020-04-01 | Hollister Incorporated | Flushable catheters |
CA2923676C (en) | 2013-12-12 | 2020-10-13 | Hollister Incorporated | Flushable catheters |
DK3079748T3 (en) | 2013-12-12 | 2020-08-17 | Hollister Inc | EXCLUSIVE DECOMPOSITION CATHETER |
US9855156B2 (en) | 2014-08-15 | 2018-01-02 | Elixir Medical Corporation | Biodegradable endoprostheses and methods of their fabrication |
US9259339B1 (en) | 2014-08-15 | 2016-02-16 | Elixir Medical Corporation | Biodegradable endoprostheses and methods of their fabrication |
US9730819B2 (en) | 2014-08-15 | 2017-08-15 | Elixir Medical Corporation | Biodegradable endoprostheses and methods of their fabrication |
US9480588B2 (en) | 2014-08-15 | 2016-11-01 | Elixir Medical Corporation | Biodegradable endoprostheses and methods of their fabrication |
US9931787B2 (en) | 2014-09-18 | 2018-04-03 | Abbott Cardiovascular Systems Inc. | Crimping polymer scaffolds |
US9795497B2 (en) | 2014-09-18 | 2017-10-24 | Abbott Cardiovascular Systems Inc. | Thermal processing of polymer scaffolds |
WO2016084087A2 (en) | 2014-11-26 | 2016-06-02 | S.T.S. Medical Ltd. | Shape change structure for treatment of nasal conditions including sinusitis |
EP3310404B1 (en) | 2015-06-17 | 2024-03-13 | Hollister Incorporated | Selectively water disintegrable materials and catheters made of such materials |
US20160374838A1 (en) * | 2015-06-29 | 2016-12-29 | Abbott Cardiovascular Systems Inc. | Drug-eluting coatings on poly(dl-lactide)-based scaffolds |
US10143573B2 (en) * | 2015-12-17 | 2018-12-04 | Abbott Cardiovascular Systems Inc. | Thin-walled scaffolds having flexible distal end |
US9956099B2 (en) | 2015-12-17 | 2018-05-01 | Abbott Cardiovascular Systems Inc. | Thin-walled scaffolds having reduced crimp profile and carrying radiopaque markers |
US9861507B2 (en) * | 2015-12-17 | 2018-01-09 | Abbott Cardiovascular Systems Inc. | Thin-walled scaffolds having modified marker structure near distal end |
US10010653B2 (en) * | 2016-02-05 | 2018-07-03 | Abbott Cardiovascular Systems Inc. | Methods for increasing coating strength to improve scaffold crimping yield |
US11622872B2 (en) | 2016-05-16 | 2023-04-11 | Elixir Medical Corporation | Uncaging stent |
CN113143536B (en) | 2016-05-16 | 2022-08-30 | 万能医药公司 | Opening support |
Family Cites Families (55)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4927838A (en) * | 1987-07-10 | 1990-05-22 | Hoffman-La Roche Inc. | Pyridine compounds which are useful in treating a disease state characterized by an excess of platelet activating factors |
JP2561853B2 (en) * | 1988-01-28 | 1996-12-11 | 株式会社ジェイ・エム・エス | Shaped memory molded article and method of using the same |
US6248129B1 (en) | 1990-09-14 | 2001-06-19 | Quanam Medical Corporation | Expandable polymeric stent with memory and delivery apparatus and method |
US5258020A (en) | 1990-09-14 | 1993-11-02 | Michael Froix | Method of using expandable polymeric stent with memory |
US5163952A (en) | 1990-09-14 | 1992-11-17 | Michael Froix | Expandable polymeric stent with memory and delivery apparatus and method |
AU650700B2 (en) | 1991-03-08 | 1994-06-30 | Keiji Igaki | Luminal stent, holding structure therefor and device for attaching luminal stent |
CA2087132A1 (en) | 1992-01-31 | 1993-08-01 | Michael S. Williams | Stent capable of attachment within a body lumen |
US5212188A (en) * | 1992-03-02 | 1993-05-18 | R. J. Reynolds Tabacco Company | Method for treatment of neurodegenerative diseases |
US5716410A (en) | 1993-04-30 | 1998-02-10 | Scimed Life Systems, Inc. | Temporary stent and method of use |
US5629077A (en) | 1994-06-27 | 1997-05-13 | Advanced Cardiovascular Systems, Inc. | Biodegradable mesh and film stent |
AU3783295A (en) | 1994-11-16 | 1996-05-23 | Advanced Cardiovascular Systems Inc. | Shape memory locking mechanism for intravascular stent |
US5616707A (en) * | 1995-01-06 | 1997-04-01 | Crooks; Peter A. | Compounds which are useful for prevention and treatment of central nervous system disorders |
US5731314A (en) * | 1995-01-06 | 1998-03-24 | Bencherif; Merouane | Pharamceutical compositions for prevention and treatment of tourette's syndrome |
US5604231A (en) * | 1995-01-06 | 1997-02-18 | Smith; Carr J. | Pharmaceutical compositions for prevention and treatment of ulcerative colitis |
US5597919A (en) * | 1995-01-06 | 1997-01-28 | Dull; Gary M. | Pyrimidinyl or Pyridinyl alkenyl amine compounds |
US5824692A (en) * | 1995-01-06 | 1998-10-20 | Lippiello; Patrick Michael | Pharmaceutical compositions for prevention and treatment of central nervous system disorders |
US5585388A (en) * | 1995-04-07 | 1996-12-17 | Sibia Neurosciences, Inc. | Substituted pyridines useful as modulators of acetylcholine receptors |
US5616717A (en) * | 1995-04-20 | 1997-04-01 | Boehringer Ingelheim Pharmaceuticals, Inc. | Process for the preparation of pure enantiomers of 1-(2-pyridyl)-2-cyclohexylethylamine |
US5616716A (en) * | 1996-01-06 | 1997-04-01 | Dull; Gary M. | (3-(5-ethoxypyridin)yl)-alkenyl 1 amine compounds |
US5663356A (en) * | 1996-04-23 | 1997-09-02 | Ruecroft; Graham | Method for preparation of aryl substituted alefinic secondary amino compounds |
US6979695B2 (en) * | 1996-04-23 | 2005-12-27 | Targacept, Inc. | Compounds capable of activating cholinergic receptors |
AU727976B2 (en) * | 1996-04-23 | 2001-01-04 | Targacept, Inc. | Pharmaceutical compositions for prevention and treatment of central nervous system disorders |
US20020052497A1 (en) * | 2000-03-09 | 2002-05-02 | Targacept, Inc. | Compounds capable of activating cholinergic receptors |
US6166048A (en) * | 1999-04-20 | 2000-12-26 | Targacept, Inc. | Pharmaceutical compositions for inhibition of cytokine production and secretion |
US5670161A (en) * | 1996-05-28 | 1997-09-23 | Healy; Kevin E. | Biodegradable stent |
US5629325A (en) * | 1996-06-06 | 1997-05-13 | Abbott Laboratories | 3-pyridyloxymethyl heterocyclic ether compounds useful in controlling chemical synaptic transmission |
US5868781A (en) * | 1996-10-22 | 1999-02-09 | Scimed Life Systems, Inc. | Locking stent |
US5833651A (en) | 1996-11-08 | 1998-11-10 | Medtronic, Inc. | Therapeutic intraluminal stents |
US5980551A (en) | 1997-02-07 | 1999-11-09 | Endovasc Ltd., Inc. | Composition and method for making a biodegradable drug delivery stent |
US5811442A (en) * | 1997-02-21 | 1998-09-22 | Bencherif; Merouane | Pharmaceutical compositions for the treatment of conditions associated with decreased blood flow |
US5861423A (en) * | 1997-02-21 | 1999-01-19 | Caldwell; William Scott | Pharmaceutical compositions incorporating aryl substituted olefinic amine compounds |
US6531606B1 (en) * | 1997-02-21 | 2003-03-11 | Targacept, Inc. | Pharmaceutical compositions incorporating aryl substituted olefinic amine compounds |
US5957975A (en) | 1997-12-15 | 1999-09-28 | The Cleveland Clinic Foundation | Stent having a programmed pattern of in vivo degradation |
PL342996A1 (en) | 1998-02-23 | 2001-07-16 | Mnemoscience Gmbh | Shape memory polymers |
HU222543B1 (en) * | 1998-02-23 | 2003-08-28 | Massachusetts Institute Of Technology | Biodegradable shape memory polymers |
US6287314B1 (en) | 1998-04-21 | 2001-09-11 | Advanced Cardiovascular Systems, Inc. | Stent deploying catheter system |
US6232316B1 (en) * | 1998-06-16 | 2001-05-15 | Targacept, Inc. | Methods for treatment of CNS disorders |
US20050131034A1 (en) * | 1998-06-16 | 2005-06-16 | Caldwell William S. | Compounds capable of activating cholinergic receptors |
US6218383B1 (en) * | 1998-08-07 | 2001-04-17 | Targacept, Inc. | Pharmaceutical compositions for the prevention and treatment of central nervous system disorders |
JP4889151B2 (en) | 1998-09-08 | 2012-03-07 | 株式会社 京都医療設計 | Vascular stent |
US6262124B1 (en) * | 1998-10-22 | 2001-07-17 | Gary Maurice Dull | Pharmaceutical compositions and methods for use |
US6455554B1 (en) * | 1999-06-07 | 2002-09-24 | Targacept, Inc. | Oxopyridinyl pharmaceutical compositions and methods for use |
US6338739B1 (en) | 1999-12-22 | 2002-01-15 | Ethicon, Inc. | Biodegradable stent |
US6527801B1 (en) | 2000-04-13 | 2003-03-04 | Advanced Cardiovascular Systems, Inc. | Biodegradable drug delivery material for stent |
US6485512B1 (en) | 2000-09-27 | 2002-11-26 | Advanced Cardiovascular Systems, Inc. | Two-stage light curable stent and delivery system |
US6607553B1 (en) | 2000-11-17 | 2003-08-19 | B. Braun Medical, Inc. | Method for deploying a thermo-mechanically expandable stent |
US7048939B2 (en) | 2001-04-20 | 2006-05-23 | The Board Of Trustees Of The Leland Stanford Junior University | Methods for the inhibition of neointima formation |
US7128755B2 (en) | 2001-06-01 | 2006-10-31 | Texas Stent Technologies, Inc. | Expandable biodegradable polymeric stents for combined mechanical support and pharmacological or radiation therapy |
WO2003011212A2 (en) | 2001-08-02 | 2003-02-13 | Cornell Research Foundation, Inc. | Biodegradable polyhydric alcohol esters |
US7572287B2 (en) * | 2001-10-25 | 2009-08-11 | Boston Scientific Scimed, Inc. | Balloon expandable polymer stent with reduced elastic recoil |
US20030216804A1 (en) | 2002-05-14 | 2003-11-20 | Debeer Nicholas C. | Shape memory polymer stent |
US20040034405A1 (en) | 2002-07-26 | 2004-02-19 | Dickson Andrew M. | Axially expanding polymer stent |
US20040045645A1 (en) * | 2002-09-10 | 2004-03-11 | Scimed Life Systems, Inc. | Shaped reinforcing member for medical device and method for making the same |
DE60336158D1 (en) * | 2002-10-11 | 2011-04-07 | Univ Connecticut | ON SEMICRISTALLINE THERMOPLASTIC POLYURETHANES BASED FOR NANOSTRUCTURED HARD SEGMENTS BASED FORM MEMORY PILARMERS |
ATE442822T1 (en) | 2004-04-02 | 2009-10-15 | Arterial Remodelling Technolog | POLYMER-BASED STENT ARRANGEMENT |
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2004
- 2004-04-02 AT AT04725381T patent/ATE442822T1/en not_active IP Right Cessation
- 2004-04-02 ES ES04725381T patent/ES2330849T3/en not_active Expired - Lifetime
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AU2004318159B2 (en) | 2011-04-07 |
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KR101098267B1 (en) | 2011-12-26 |
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