WO2007005246A1 - Stent fixture and method for reducing coating defects - Google Patents
Stent fixture and method for reducing coating defects Download PDFInfo
- Publication number
- WO2007005246A1 WO2007005246A1 PCT/US2006/023636 US2006023636W WO2007005246A1 WO 2007005246 A1 WO2007005246 A1 WO 2007005246A1 US 2006023636 W US2006023636 W US 2006023636W WO 2007005246 A1 WO2007005246 A1 WO 2007005246A1
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- WIPO (PCT)
- Prior art keywords
- stent
- fixture
- arm elements
- mandrel
- elements
- Prior art date
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Classifications
-
- 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
- A61L31/082—Inorganic materials
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B05—SPRAYING OR ATOMISING IN GENERAL; APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
- B05B—SPRAYING APPARATUS; ATOMISING APPARATUS; NOZZLES
- B05B13/00—Machines or plants for applying liquids or other fluent materials to surfaces of objects or other work by spraying, not covered by groups B05B1/00 - B05B11/00
- B05B13/02—Means for supporting work; Arrangement or mounting of spray heads; Adaptation or arrangement of means for feeding work
- B05B13/0221—Means for supporting work; Arrangement or mounting of spray heads; Adaptation or arrangement of means for feeding work characterised by the means for moving or conveying the objects or other work, e.g. conveyor belts
- B05B13/0228—Means for supporting work; Arrangement or mounting of spray heads; Adaptation or arrangement of means for feeding work characterised by the means for moving or conveying the objects or other work, e.g. conveyor belts the movement of the objects being rotative
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
Definitions
- This invention relates generally to stent fixtures, and more particularly, but not exclusively, provides a stent fixture and method for reducing coating defects on stents.
- Blood vessel occlusions are commonly treated by mechanically enhancing blood flow in the affected vessels, such as by employing a stent.
- Stents act as scaffoldings, functioning to physically hold open and, if desired, to expand the wall of affected vessels.
- stents are capable of being compressed, so that they can be inserted through small lumens via catheters, and then expanded to a larger diameter once they are at the desired location.
- Examples in the patent literature disclosing stents include U.S. Patent
- Patent No. 4,886,062 issued to Wiktor.
- FIG. 1 illustrates a conventional stent 10 formed from a plurality of struts 12.
- the plurality of struts 12 are radially expandable and interconnected by comiecting elements 14 that are disposed between the adjacent struts 12, leaving lateral openings or gaps 16 between the adjacent struts 12.
- the struts 12 and the connecting elements 14 define a tubular stent body having an outer, tissue-contacting surface and an inner surface.
- Stents are used not only for mechanical intervention but also as vehicles for providing biological therapy. Biological therapy can be achieved by medicating the stents.
- Medicated stents provide for the local administration of a therapeutic substance at the diseased site. Local delivery of a therapeutic substance is a preferred method of treatment because the substance is concentrated at a specific site and thus smaller total levels of medication can be administered in comparison to systemic dosages that often produce adverse or even toxic side effects for the patient.
- One method of medicating a stent involves the use of a polymeric carrier coated onto the surface of the stent.
- a composition including a solvent, a polymer dissolved in the solvent, and a therapeutic substance dispersed in the blend is applied to the stent by immersing the stent in the composition or by spraying the composition onto the stent.
- the solvent is allowed to evaporate, leaving on the stent strut surfaces a coating of the polymer and the therapeutic substance impregnated in the polymer.
- a high degree of surface contact between the stent and the supporting apparatus can provide regions in which the liquid composition can flow, wick, and collect as the composition is applied.
- the excess composition hardens to form excess coating at and around the contact points between the stent and the supporting apparatus.
- the excess coating may stick to the apparatus, thereby removing some of the coating from the stent and leaving bare areas.
- the excess coating may stick to the stent, thereby leaving excess coating as clumps or pools on the struts or webbing between the struts.
- a stent fixture for supporting a stent during formation of a coating comprising a structure having arm elements extending from the structure.
- the arm elements can be are configured to allow an inner side of a stent to rest on and be supported by the arm elements.
- the structure can support one end of the stent such that the fixture can, in some embodiments, additionally comprise a second structure for support an opposing end of the stent.
- the second structure can comprise arm elements extending out from the second structure.
- the arm elements of the second structure are configured to allow the inner side of the stent to rest on and be supported by the arm elements of the second structure.
- the fixture can include a third structure connecting the structure to the second structure and extending through a longitudinal bore of the stent. The stent can be securely pinched between the plurality of arm elements of the structures.
- FIG. 1 is a diagram illustrating a conventional stent
- FIG. 2 is a diagram illustrating a stent fixture in accordance with an embodiment of the invention
- FIG. 3 is a diagram illustrating a disassembled view of stent fixture of FIG. 2;
- FIG. 4 is a diagram illustrating a front view of a support member of the stent fixture of FIG. 2;
- FIG. 5 is a diagram illustrating a perspective view of the support member
- FIG. 6 is a diagram illustrating a stent mounted on the support member
- FIG. 7 is a diagram illustrating a support member and locking member according to another embodiment of the invention.
- FIG. 8 is a diagram illustrating a support member according to another embodiment of the invention.
- FIG. 9 is a diagram illustrating a stent mounted to the support member of FIG. 8;
- FIG. 10 is a flowchart illustrating a method of coating a stent
- FIG. 11 is a diagram illustrating a stent coated using the stent mandrel fixture of FIG. 3.
- FIG. 2 illustrates a stent mandrel fixture 20 in accordance with an embodiment of the invention.
- the fixture 20 for supporting the stent 10 is illustrated to include a support member 22, a mandrel 24, and a lock member 26.
- the support member 22 can connect to a motor 30A so as to provide rotational motion about the longitudinal axis of the stent 10, as depicted by arrow 32, during a coating process.
- a motor 30A can also be provided for moving the support member 22 in a linear direction, back and forth, along a rail 34.
- FIG. 3 illustrates a disassembled view of the stent mandrel fixture 20.
- the support member 22, can have a generally cylindrical body and an end wall 23 which faces an end of a stent.
- the end wall 23 can include a recess 25 defining an edge rim or lip protruding around the circumference of the end wall 23.
- a plurality of elements, support arms or wires 36 extend out from the perimeter of the support member 22, more particularly from the end wall 23.
- the elements 36 extend out from the edge rim.
- the elements 36 can be, in
- angle ⁇ i can be about 45°. If the elements are extending from edge rim of the end wall 23, an inner side of the edge rim can be slanted to accommodate for this tilt.
- the elements 36 can converge inwardly from an edge of the end wall 23 of the support member towards the center of the end wall 23. As is best illustrated by the figures, the elements 36 do not contact one another and allow for a sufficient entry space for the mandrel 24 to extend out from the support member 22. In other words, the spacing between the end tips of the elements 36 should be at least as wide as the diameter of the mandrel 24 used, hi some embodiments, the end tip of the elements 36 can contact the mandrel 24.
- the end tips of the elements 36 converge but yet remain spaced from the mandrel 24.
- the elements 36 can extend at least partially over the mandrel 24 and can prevent a stent from making contact with the mandrel.
- the elements 36 can also prevent the support member 22 from making contact with an end ring of the stent.
- the elements, wires or support arms 36 can be rigidly coupled to the support member 22 so as not be capable of pivoting about a juncture, bending or flexing when a stent is positioned thereon and/or during a coating process.
- elements 36 can have at least a partial "give" in the form of bending, flexing or pivoting.
- At least one of the elements can be rigid while at least one is flexible, bendable or pivotable.
- FIG 3 illustrates 3 elements, wires or support arms 36.
- the numbers can be 2, 3, 5, 6, 7 or 8. Although more than 8 can be used, it may provide for excessive contact points leading to coating defects while on the other hand the amount of support is not necessarily better.
- the mandrel 24 can be permanently affixed to the support member 22.
- the support member 22 can include a bore 38 for receiving a first end 40 of the mandrel 24.
- the first end 40 of the mandrel 24 can be threaded to screw into the bore 38 or, alternatively, can be retained within the bore 38 by a friction fit.
- the bore 38 should be deep enough so as to allow the mandrel 24 to securely mate with the support member 22.
- the depth of the bore 38 can also be over-extended so as to allow a significant length of the mandrel 24 to penetrate or screw into the bore 38.
- the bore 38 can also extend completely through the support member 22. This would allow the length of the mandrel 24 to be adjusted to accommodate stents of various sizes.
- the outer diameter of the mandrel 24 can be smaller than the inner diameter of the stent 10, as positioned on the fixture, such that the elements 36 prevent the outer surface of the mandrel 24 from making contact with the inner surface of the stent 10.
- a sufficient clearance between the outer surface of the mandrel 24 and the inner surface of the stent 10 should be provided to prevent the mandrel 24 from obstructing the pattern of the stent body during the coating process.
- the outer diameter of the mandrel 24 can be from about 0.010 inches to about 0.040 inches when the stent 10 has an inner diameter of between about 0.025 inches and about 0.065 inches, e.g., for a coronary stent.
- the mandrel 24 can have larger diameters
- the lock member 26 can be identical or generally similar to the support member 22.
- the lock member 26 includes a plurality of elements, support arms or wires 42 extending out from an end wall 27 of the cylindrical body of the lock member 26.
- elements 42 of the lock member 26 can be rigid, flexible, bendable, pivotable or any combination.
- elements 36 can be more or less flexible, bendable or pivotably than the elements 42 of the lock member 26.
- the degree of fexiblity or rigidness is the same.
- elements 42 can have an
- Angle ⁇ 2 can be the same as or different than the above-
- a second end 44 of the mandrel 24 can be permanently affixed to the lock member 26 if the end 40 is disengagable from the support member 22.
- the mandrel 24 can have a threaded second end 44 for screwing into a bore 46 of the lock member 26.
- the bore 46 can be of any suitable depth that would allow the lock member 26 to be incrementally moved closer to the support member 22.
- the bore 46 can also extend completely through the lock member 26.
- the stents 10 of any length can be securely pinched between the support and the lock members 22 and 26.
- a non-threaded second end 44 and the bore 46 combination is employed such that the second end 44 can be press-fitted or friction-fitted within the bore 46 to prevent movement of the stent 10 on the stent mandrel fixture 20.
- the stent 10 rests on and/or is supported by the elements, support arms or wires 36 and 42, as will be discussed in further detail in conjunction with FIG. 6 and FIG. 9 below.
- the elements, support arms or wires 36 and 42 may have diameters of about 0.004 inches to about 0.006 inches.
- the diameter of the wires is of sufficient size so as to allow for the wires to be fittingly placed in a crown of the end rings of a stent, as is best illustrated by FIG. 6.
- an end ring of a stent can have a "V" shape, a "U” shape, a unique configuration to the struts.
- the elements 36 and 42 can be of small enough diameter so as to be placed at least partially in between the strut bodies or the space between two segments of the struts. As such, the stent 10 is only in contact with the elements, support arms or wires 36 and 42 and therefore provides minimal contact area for the collection of excess coating, thereby minimizing the formation of clumps, which can lead to further defects, such as tears and rough surfaces, when the stent 10 is removed from the fixture 20. Ih order to further reduce coating defects, the elements, support arms or wires 36 and 42 may be coated with or made of, via injection molding, one or more polymeric materials having less adhesive force with the coating substance than with the elements, support arms or wires 36 and 42.
- a suitable polymeric materials include poly (tetrafluoroethylene) (e.g., TEFLON), fluorinated ethylene propylene (“FEP”), poly (vinylidene fluoride) (“PVDF”), poly (para -xylyene), polyolefins (e.g., high density poly (ethylene) and poly (propylene)), and ME92 coating from ME92 Operations, Inc. of Buffalo, RI.
- the elements, support arms or wires 36 and 42 may be made of one or more of the non-stick polymeric materials.
- the components of the coating substance or composition can include a solvent or a solvent system comprising multiple solvents, a polymer or a combination of polymers, a therapeutic substance or a drug or a combination of drugs.
- the coating substance can be exclusively a polymer or a combination of polymers (e.g., for application of a primer layer or topcoat layer).
- the coating substance can be a drug that is polymer free.
- Polymers can be biostable, bioabsorbable, biodegradable, or bioerodable. Biostable refers to polymers that are not biodegradable.
- biodegradable, bioabsorbable, and bioerodable are used interchangeably and refer to polymers that are capable of being completely degraded and/or eroded when exposed to bodily fluids such as blood and can be gradually resorbed, absorbed, and/or eliminated by the body.
- the processes of breaking down and eventual absorption and elimination of the polymer can be caused by, for example, hydrolysis, metabolic processes, bulk or surface erosion, and the like.
- polymers that may be used include, but are not limited to, poly(N-acetylglucosamine) (Chitin), Chitoson, poly(hydroxyvalerate), poly(lactide-co- glycolide), poly(hydroxybutyrate), poly(hydroxybutyrate-co-valerate), polyorthoester, polyanhydride, poly(glycolic acid), poly(glycolide), poly(L-lactic acid), ⁇ oly(L-lactide), poly(D,L-lactic acid), poly(D,L-lactide), poly(D-lactic acid), poly(D-lactide), poly(caprolactone), poly(trimethylene carbonate), polyester amide, poly(glycolic acid-co- trimethylene carbonate), co-poly(ether-esters) (e.g.
- PEO/PLA polyphosphazenes
- biomolecules such as fibrin, fibrinogen, cellulose, starch, collagen and hyaluronic acid
- polyurethanes silicones
- polyesters polyolefins, polyisobutylene and ethylene- alphaolefin copolymers
- acrylic polymers and copolymers other than polyacrylates vinyl halide polymers and copolymers (such as polyvinyl chloride), polyvinyl ethers (such as polyvinyl methyl ether), polyvinylidene halides (such as polyvinylidene chloride), polyacrylonitrile, polyvinyl ketones, polyvinyl aromatics (such as polystyrene), polyvinyl esters (such as polyvinyl acetate), acrylonitrile-styrene copolymers, ABS resins, polyamides (such as Nylon 66 and polycaprolactam), polycarbonates, polyoxymethylenes, polyimides,
- EVAL ethylene vinyl alcohol copolymer
- poly(butyl methacrylate) poly(vinylidene fiuoride-co- hexafluororpropene)
- SOLEF 21508 available from Solvay Solexis PVDF, Thorofare, NJ
- polyvinylidene fluoride otherwise known as KYNAR, available from ATOFES
- solvent is defined as a liquid substance or composition that is compatible with the polymer and/or drug and is capable of dissolving the polymer and/or drug at the concentration desired in the composition.
- solvents include, but are not limited to, dimethylsulfoxide, chloroform, acetone, water (buffered saline), xylene, methanol, ethanol, 1-propaiiol, tetrahydrofuran, 1 -butanone, dimethylformamide, dimethylacetamide, cyclohexanone, ethyl acetate, methylethyllcetone, propylene glycol monomethylether, isopropanol, isopropanol admixed with water, N-methyl pyrrolidinone, toluene, and mixtures and combinations thereof.
- the therapeutic substance or drug can include any substance capable of exerting a therapeutic or prophylactic effect.
- active agents include antiproliferative substances such as actinomycin D, or derivatives and analogs thereof (manufactured by Sigma-Aldrich 1001 West Saint Paul Avenue, Milwaukee, WI 53233; or COSMEGEN available from Merck). Synonyms of actinomycin D include dactinomycin, actinomycin rV, actinomycin I 1 , actinomycin X 1 , and actinomycin C 1 .
- the bioactive agent can also fall under the genus of antineoplastic, anti-inflammatory, antiplatelet, anticoagulant, antifibrin, antithrombin, antimitotic, antibiotic, antiallergic and antioxidant substances.
- antineoplastics and/or antimitotics examples include paclitaxel, (e.g., TAXOL ® by Bristol-Myers Squibb Co., Stamford, Conn.), docetaxel (e.g., Taxotere ® , from Aventis S.A., Frankfurt, Germany), methotrexate, azathioprine, vincristine, vinblastine, fluorouracil, doxorubicin hydrochloride (e.g., Adriamycin ® from Pharmacia & Upjohn, Peapack N. J.), and mitomycin (e.g., Mutamycin ® from Bristol-Myers Squibb Co., Stamford, Conn.).
- paclitaxel e.g., TAXOL ® by Bristol-Myers Squibb Co., Stamford, Conn.
- docetaxel e.g., Taxotere ® , from Aventis S.A., Frankfurt, Germany
- antiplatelets examples include aspirin, sodium heparin, low molecular weight heparins, heparinoids, hirudin, argatroban, forskolin, vapiprost, prostacyclin and prostacyclin analogues, dextran, D-phe-pro-arg-chloromethylketone (synthetic antithrombin), dipyridamole, glycoprotein Ilb/IIIa platelet membrane receptor antagonist antibody, recombinant hirudin, and thrombin inhibitors such as Angiomax a (Biogen, Inc., Cambridge, Mass.).
- cytostatic or antiproliferative agents examples include angiopeptin, angiotensin converting enzyme inhibitors such as captopril (e.g., Capoten ® and Capozide ® from Bristol-Myers Squibb Co., Stamford, Conn.), cilazapril or lisinopril (e.g., Prinivil ® and Prinzide ® from Merck & Co., Inc., Whitehouse Station, NJ), calcium channel blockers (such as nifedipine), colchicine, proteins, peptides, fibroblast growth factor (FGF) antagonists, fish oil (omega 3 -fatty acid), histamine antagonists, lovastatin (an inhibitor of HMG-CoA reductase, a cholesterol lowering drug, brand name Mevacor ® from Merck & Co., Inc., Whitehouse Station, NJ), monoclonal antibodies (such as those specific for Platelet-Derived Growth Factor (PDGF) receptors),
- an antiallergic agent is permirolast potassium.
- Other therapeutic substances or agents which may be appropriate agents include cisplatin, insulin sensitizers, receptor tyrosine kinase inhibitors, carboplatin, alpha-interferon, genetically engineered epithelial cells, steroidal anti-inflammatory agents, non-steroidal antiinflammatory agents, antivirals, anticancer drugs, anticoagulant agents, free radical scavengers, estradiol, antibiotics, nitric oxide donors, super oxide dismutases, super oxide dismutases mimics, 4-amino-2,2,6,6-tetramethylpiperidine-l-oxyl (4-amino-TEMPO), tacrolimus, dexamethasone, ABT-578, clobetasol, cytostatic agents, prodrugs thereof, co- drugs thereof, and a combination thereof.
- FIG. 4 is a diagram illustrating a front view of the end wall 23 of the support
- the plurality of elements, support arms or wires 36 includes
- the plurality of wires 36 extend from the circumference of the support member 22 to the bore 38. In other embodiments, the
- plurality of wires 36 can be spaced apart differently and/or comprise a different number
- FIG. 5 is a diagram illustrating a perspective view of the support member 22
- the plurality of wires 36 may have pointed ends such that the sections of the ends facing the mandrel 24 run parallel with the mandrel 24, which enables a smoother fit between
- FIG. 6 is a diagram illustrating the stent 10 mounted on the stent mandrel fixture
- the elements, support arms or wires 36 and 42 contact the mandrel and the stent 10 is supported by the wires 36 as well as the wires 42.
- the stent 10 only interfaces with the stent mandrel fixture 20 at six minute points
- the support member 22 can
- lock pin 65 that extends from a surface of the member 22 through to the
- FIG. 7 is a diagram illustrating a support member 22 and a locking member 26
- locking member 26 each have two wires extending there from.
- FIG. 8 and FIG. 9 are diagrams illustrating a support member 22 according to another embodiment of the invention.
- the support member 22 of FIG. 8 and FIG. 9 has a plurality of elements, support arms or wires (e.g., 3) 52 extending laterally from the support member 22.
- the elements can extend parallel to the longitudinal axis of a stent or parallel to the longitudinal axis of the mandrel 24.
- the elements, support arms or wires 52 may be about 4 to about 8 mm in length and about 0.004 to about 0.008 inches in diameter.
- the elements, support arms or wires 52 each have a sphere 54 at their respective ends.
- the spheres 54 are large enough so as to prevent the inner side of a stent from making contact with the element 52.
- the size of the spheres 54 should be larger than a gap between the struts under which the spheres are placed and small enough so that no portion of the spheres 52 protrudes out of the outer surface of the stent.
- a portion of the spheres can protrude out from the outer surface of the stent.
- the spheres 54 can each have a diameter of about 0.015 to about 0.020 of an inch.
- the spheres 54 provide more rigid support than the wires 36 or 42 but provide more contact surface for a coating composition to pool, thereby slightly increasing the possibility of coating defects but still providing less surface area than conventional stent mounting fixtures.
- FIG. 10 is a flowchart illustrating a method 1000 of coating a stent. First a stent 10 is mounted (1010) on the stent mandrel fixture 20.
- Mounting (1010) can include rotating the support member 22 vertically, inserting the mandrel 24 into the bore 38, mounting the stent 10 on the wires 36 or 52, and repeating for the lock member 26.
- a high magnification video device can also be used during the mounting (1010) to assist in . adjusting the contact position between the wires 36 or 52 and the stent 10.
- the stent 10 is then rotated and/or translated (1020) and a coating is sprayed (1030) on the stent 10 during the rotation (1020).
- the rotation ratio of the mandrel and stent is 1:1 considering how elements 36 and 42 engage and rotate the stent.
- Air or gas can be applied (1040) to the stent for drying during and/or subsequent to the application of the coating composition. Acts of spraying and blowing can be repeated if desired (1050).
- the method 1000 then ends.
- FIG. 11 is a diagram illustrating a stent 10 coated using the stent mandrel fixture 20. As can be seen, there are no defects, such as inner diameter tearing, rough surfaces, cob webs, etc., at the end of the stent 10.
- the plurality of wires 52 may also be coated with a non-stick polymeric material having less adhesive force with the coating substance than with the members.
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Abstract
A stent fixture for supporting a stent during formation of a coating is provided. The fixture comprising two supports (22,26) having extending elements (36,42) for contacting the stent. As the extending elements (36,42) provide the only contact points for the stent coating defects are reduced.
Description
STENT FIXTURE AND METHOD FOR REDUCING COATING DEFECTS
Technical Field
This invention relates generally to stent fixtures, and more particularly, but not exclusively, provides a stent fixture and method for reducing coating defects on stents.
Background Blood vessel occlusions are commonly treated by mechanically enhancing blood flow in the affected vessels, such as by employing a stent. Stents act as scaffoldings, functioning to physically hold open and, if desired, to expand the wall of affected vessels.
Typically stents are capable of being compressed, so that they can be inserted through small lumens via catheters, and then expanded to a larger diameter once they are at the desired location. Examples in the patent literature disclosing stents include U.S. Patent
No. 4,733,665 issued to Palmaz, U.S. Patent No. 4,800,882 issued to Gianturco, and U.S.
Patent No. 4,886,062 issued to Wiktor.
FIG. 1 illustrates a conventional stent 10 formed from a plurality of struts 12. The plurality of struts 12 are radially expandable and interconnected by comiecting elements 14 that are disposed between the adjacent struts 12, leaving lateral openings or gaps 16 between the adjacent struts 12. The struts 12 and the connecting elements 14 define a tubular stent body having an outer, tissue-contacting surface and an inner surface. Stents are used not only for mechanical intervention but also as vehicles for providing biological therapy. Biological therapy can be achieved by medicating the stents. Medicated stents provide for the local administration of a therapeutic substance at the diseased site. Local delivery of a therapeutic substance is a preferred method of
treatment because the substance is concentrated at a specific site and thus smaller total levels of medication can be administered in comparison to systemic dosages that often produce adverse or even toxic side effects for the patient.
One method of medicating a stent involves the use of a polymeric carrier coated onto the surface of the stent. A composition including a solvent, a polymer dissolved in the solvent, and a therapeutic substance dispersed in the blend is applied to the stent by immersing the stent in the composition or by spraying the composition onto the stent. The solvent is allowed to evaporate, leaving on the stent strut surfaces a coating of the polymer and the therapeutic substance impregnated in the polymer. A shortcoming of the above-described method of medicating a stent is the potential for coating defects. While some coating defects can be minimized by adjusting the coating parameters, other defects occur due to the nature of the interface between the stent and the apparatus on which the stent is supported during the coating process. A high degree of surface contact between the stent and the supporting apparatus can provide regions in which the liquid composition can flow, wick, and collect as the composition is applied. As the solvent evaporates, the excess composition hardens to form excess coating at and around the contact points between the stent and the supporting apparatus. Upon the removal of the coated stent from the supporting apparatus, the excess coating may stick to the apparatus, thereby removing some of the coating from the stent and leaving bare areas. Alternatively, the excess coating may stick to the stent, thereby leaving excess coating as clumps or pools on the struts or webbing between the struts.
Accordingly, a new stent fixture and method of use are needed to minimize coating defects.
SUMMARY
In accordance with one embodiment a stent fixture for supporting a stent during formation of a coating is provided comprising a structure having arm elements extending from the structure. The arm elements can be are configured to allow an inner side of a stent to rest on and be supported by the arm elements. The structure can support one end of the stent such that the fixture can, in some embodiments, additionally comprise a second structure for support an opposing end of the stent. The second structure can comprise arm elements extending out from the second structure. The arm elements of the second structure are configured to allow the inner side of the stent to rest on and be supported by the arm elements of the second structure. In some embodiments, the fixture can include a third structure connecting the structure to the second structure and extending through a longitudinal bore of the stent. The stent can be securely pinched between the plurality of arm elements of the structures.
In accordance with another aspect of the invention, methods of coating a stent using the above-described fixtures are provided.
BRIEF DESCRIPTION OF THE DRAWINGS
Non-limiting and non-exhaustive embodiments of the present invention are described with reference to the following figures, wherein like reference numerals refer to like parts throughout the various views unless otherwise specified. FIG. 1 is a diagram illustrating a conventional stent;
FIG. 2 is a diagram illustrating a stent fixture in accordance with an embodiment of the invention;
FIG. 3 is a diagram illustrating a disassembled view of stent fixture of FIG. 2;
FIG. 4 is a diagram illustrating a front view of a support member of the stent fixture of FIG. 2;
FIG. 5 is a diagram illustrating a perspective view of the support member;
FIG. 6 is a diagram illustrating a stent mounted on the support member;
FIG. 7 is a diagram illustrating a support member and locking member according to another embodiment of the invention; FIG. 8 is a diagram illustrating a support member according to another embodiment of the invention;
FIG. 9 is a diagram illustrating a stent mounted to the support member of FIG. 8;
FIG. 10 is a flowchart illustrating a method of coating a stent;
FIG. 11 is a diagram illustrating a stent coated using the stent mandrel fixture of FIG. 3.
DETAILED DESCRIPTION
The following description is provided to enable any person having ordinary skill in the art to make and use the invention, and is provided in the context of a particular application and its requirements. Various modifications to the embodiments will be readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other embodiments and applications without departing from the spirit and scope of the invention. Thus, the present invention is not intended to be limited to the embodiments shown, but is to be accorded the widest scope consistent with the principles, features and teachings disclosed herein. FIG. 2 illustrates a stent mandrel fixture 20 in accordance with an embodiment of the invention. The fixture 20 for supporting the stent 10 is illustrated to include a support member 22, a mandrel 24, and a lock member 26. The support member 22 can connect to a motor 30A so as to provide rotational motion about the longitudinal axis of the stent 10, as depicted by arrow 32, during a coating process. Another motor 30B can also be provided for moving the support member 22 in a linear direction, back and forth, along a rail 34.
FIG. 3 illustrates a disassembled view of the stent mandrel fixture 20. The support member 22, can have a generally cylindrical body and an end wall 23 which faces an end of a stent. In some embodiments, as best illustrated by FIG. 5, the end wall 23 can include a recess 25 defining an edge rim or lip protruding around the circumference of the end wall 23. A plurality of elements, support arms or wires 36 extend out from the perimeter of the support member 22, more particularly from the end wall 23. In some embodiments, the elements 36 extend out from the edge rim. The elements 36 can be, in
some embodiments, tapering inwardly at an angle <jn of about 15° to about 75°, more
narrowly from about 30° to about 60°. By way of example, angle φi can be about 45°. If
the elements are extending from edge rim of the end wall 23, an inner side of the edge rim can be slanted to accommodate for this tilt. The elements 36 can converge inwardly from an edge of the end wall 23 of the support member towards the center of the end wall 23. As is best illustrated by the figures, the elements 36 do not contact one another and allow for a sufficient entry space for the mandrel 24 to extend out from the support member 22. In other words, the spacing between the end tips of the elements 36 should be at least as wide as the diameter of the mandrel 24 used, hi some embodiments, the end tip of the elements 36 can contact the mandrel 24. In other embodiments, the end tips of the elements 36 converge but yet remain spaced from the mandrel 24. The elements 36 can extend at least partially over the mandrel 24 and can prevent a stent from making contact with the mandrel. The elements 36 can also prevent the support member 22 from making contact with an end ring of the stent. The elements, wires or support arms 36 can be rigidly coupled to the support member 22 so as not be capable of pivoting about a juncture, bending or flexing when a stent is positioned thereon and/or during a coating process. Alternatively, elements 36 can have at least a partial "give" in the form of bending, flexing or pivoting. In some embodiments, at least one of the elements can be rigid while at least one is flexible, bendable or pivotable. FIG 3 illustrates 3 elements, wires or support arms 36. In some embodiments, the numbers can be 2, 3, 5, 6, 7 or 8. Although more than 8 can be used, it may provide for excessive contact points leading to coating defects while on the other hand the amount of support is not necessarily better.
In accordance with one embodiment of the invention, the mandrel 24 can be permanently affixed to the support member 22. Alternatively, the support member 22 can include a bore 38 for receiving a first end 40 of the mandrel 24. The first end 40 of the mandrel 24 can be threaded to screw into the bore 38 or, alternatively, can be retained within the bore 38 by a friction fit. The bore 38 should be deep enough so as to allow the
mandrel 24 to securely mate with the support member 22. The depth of the bore 38 can also be over-extended so as to allow a significant length of the mandrel 24 to penetrate or screw into the bore 38. The bore 38 can also extend completely through the support member 22. This would allow the length of the mandrel 24 to be adjusted to accommodate stents of various sizes.
The outer diameter of the mandrel 24 can be smaller than the inner diameter of the stent 10, as positioned on the fixture, such that the elements 36 prevent the outer surface of the mandrel 24 from making contact with the inner surface of the stent 10. A sufficient clearance between the outer surface of the mandrel 24 and the inner surface of the stent 10 should be provided to prevent the mandrel 24 from obstructing the pattern of the stent body during the coating process. By way of example, the outer diameter of the mandrel 24 can be from about 0.010 inches to about 0.040 inches when the stent 10 has an inner diameter of between about 0.025 inches and about 0.065 inches, e.g., for a coronary stent. For a peripheral stent having a larger diameter, the mandrel 24 can have larger diameters, In some embodiments, the lock member 26 can be identical or generally similar to the support member 22. In some embodiments, the lock member 26 includes a plurality of elements, support arms or wires 42 extending out from an end wall 27 of the cylindrical body of the lock member 26. As with the elements 36 of the support member 22, elements 42 of the lock member 26 can be rigid, flexible, bendable, pivotable or any combination. In some embodiments, elements 36 can be more or less flexible, bendable or pivotably than the elements 42 of the lock member 26. Preferably, the degree of fexiblity or rigidness is the same. In some embodiments, elements 42 can have an
inwardly tapered angle φ2. Angle φ2 can be the same as or different than the above-
described angle φ1. Although 3 elements 42 have been illustrated, any suitable number such as 2, 4, 5, 6, 7, and 8 can be used. More than 8 can be used but may increase the
contact areas between a stent and elements 42. A second end 44 of the mandrel 24 can be permanently affixed to the lock member 26 if the end 40 is disengagable from the support member 22. Alternatively, in accordance with another embodiment, the mandrel 24 can have a threaded second end 44 for screwing into a bore 46 of the lock member 26. The bore 46 can be of any suitable depth that would allow the lock member 26 to be incrementally moved closer to the support member 22. The bore 46 can also extend completely through the lock member 26. Accordingly, the stents 10 of any length can be securely pinched between the support and the lock members 22 and 26. In accordance with yet another embodiment, a non-threaded second end 44 and the bore 46 combination is employed such that the second end 44 can be press-fitted or friction-fitted within the bore 46 to prevent movement of the stent 10 on the stent mandrel fixture 20.
During a spray coating process, the stent 10 rests on and/or is supported by the elements, support arms or wires 36 and 42, as will be discussed in further detail in conjunction with FIG. 6 and FIG. 9 below. In an embodiment of the invention, the elements, support arms or wires 36 and 42 may have diameters of about 0.004 inches to about 0.006 inches. In some embodiments, the diameter of the wires is of sufficient size so as to allow for the wires to be fittingly placed in a crown of the end rings of a stent, as is best illustrated by FIG. 6. For example, an end ring of a stent can have a "V" shape, a "U" shape, a unique configuration to the struts. The elements 36 and 42 can be of small enough diameter so as to be placed at least partially in between the strut bodies or the space between two segments of the struts. As such, the stent 10 is only in contact with the elements, support arms or wires 36 and 42 and therefore provides minimal contact area for the collection of excess coating, thereby minimizing the formation of clumps, which can lead to further defects, such as tears and rough surfaces, when the stent 10 is removed from the fixture 20.
Ih order to further reduce coating defects, the elements, support arms or wires 36 and 42 may be coated with or made of, via injection molding, one or more polymeric materials having less adhesive force with the coating substance than with the elements, support arms or wires 36 and 42. Examples of a suitable polymeric materials include poly (tetrafluoroethylene) (e.g., TEFLON), fluorinated ethylene propylene ("FEP"), poly (vinylidene fluoride) ("PVDF"), poly (para -xylyene), polyolefins (e.g., high density poly (ethylene) and poly (propylene)), and ME92 coating from ME92 Operations, Inc. of Providence, RI. In an alternative embodiment of the invention, the elements, support arms or wires 36 and 42 may be made of one or more of the non-stick polymeric materials.
The components of the coating substance or composition can include a solvent or a solvent system comprising multiple solvents, a polymer or a combination of polymers, a therapeutic substance or a drug or a combination of drugs. In some embodiments, the coating substance can be exclusively a polymer or a combination of polymers (e.g., for application of a primer layer or topcoat layer). In some embodiments, the coating substance can be a drug that is polymer free. Polymers can be biostable, bioabsorbable, biodegradable, or bioerodable. Biostable refers to polymers that are not biodegradable. The terms biodegradable, bioabsorbable, and bioerodable are used interchangeably and refer to polymers that are capable of being completely degraded and/or eroded when exposed to bodily fluids such as blood and can be gradually resorbed, absorbed, and/or eliminated by the body. The processes of breaking down and eventual absorption and elimination of the polymer can be caused by, for example, hydrolysis, metabolic processes, bulk or surface erosion, and the like.
Representative examples of polymers that may be used include, but are not limited to, poly(N-acetylglucosamine) (Chitin), Chitoson, poly(hydroxyvalerate), poly(lactide-co- glycolide), poly(hydroxybutyrate), poly(hydroxybutyrate-co-valerate), polyorthoester, polyanhydride, poly(glycolic acid), poly(glycolide), poly(L-lactic acid), ρoly(L-lactide), poly(D,L-lactic acid), poly(D,L-lactide), poly(D-lactic acid), poly(D-lactide), poly(caprolactone), poly(trimethylene carbonate), polyester amide, poly(glycolic acid-co- trimethylene carbonate), co-poly(ether-esters) (e.g. PEO/PLA), polyphosphazenes, biomolecules (such as fibrin, fibrinogen, cellulose, starch, collagen and hyaluronic acid), polyurethanes, silicones, polyesters, polyolefins, polyisobutylene and ethylene- alphaolefin copolymers, acrylic polymers and copolymers other than polyacrylates, vinyl halide polymers and copolymers (such as polyvinyl chloride), polyvinyl ethers (such as polyvinyl methyl ether), polyvinylidene halides (such as polyvinylidene chloride), polyacrylonitrile, polyvinyl ketones, polyvinyl aromatics (such as polystyrene), polyvinyl esters (such as polyvinyl acetate), acrylonitrile-styrene copolymers, ABS resins, polyamides (such as Nylon 66 and polycaprolactam), polycarbonates, polyoxymethylenes, polyimides, polyethers, polyurethanes, rayon, rayon-triacetate, cellulose, cellulose acetate, cellulose butyrate, cellulose acetate butyrate, cellophane, cellulose nitrate, cellulose propionate, cellulose ethers, and carboxymethyl cellulose. Representative examples of polymers that may be especially well suited for use include ethylene vinyl alcohol copolymer (commonly known by the generic name EVOH or by the trade name EVAL), poly(butyl methacrylate), poly(vinylidene fiuoride-co- hexafluororpropene) (e.g., SOLEF 21508, available from Solvay Solexis PVDF, Thorofare, NJ), polyvinylidene fluoride (otherwise known as KYNAR, available from ATOFESfA Chemicals, Philadelphia, PA), ethylene- vinyl acetate copolymers, and polyethylene glycol.
"Solvent" is defined as a liquid substance or composition that is compatible with the polymer and/or drug and is capable of dissolving the polymer and/or drug at the concentration desired in the composition. Examples of solvents include, but are not limited to, dimethylsulfoxide, chloroform, acetone, water (buffered saline), xylene, methanol, ethanol, 1-propaiiol, tetrahydrofuran, 1 -butanone, dimethylformamide, dimethylacetamide, cyclohexanone, ethyl acetate, methylethyllcetone, propylene glycol monomethylether, isopropanol, isopropanol admixed with water, N-methyl pyrrolidinone, toluene, and mixtures and combinations thereof.
The therapeutic substance or drug can include any substance capable of exerting a therapeutic or prophylactic effect. Examples of active agents include antiproliferative substances such as actinomycin D, or derivatives and analogs thereof (manufactured by Sigma-Aldrich 1001 West Saint Paul Avenue, Milwaukee, WI 53233; or COSMEGEN available from Merck). Synonyms of actinomycin D include dactinomycin, actinomycin rV, actinomycin I1, actinomycin X1, and actinomycin C1. The bioactive agent can also fall under the genus of antineoplastic, anti-inflammatory, antiplatelet, anticoagulant, antifibrin, antithrombin, antimitotic, antibiotic, antiallergic and antioxidant substances. Examples of such antineoplastics and/or antimitotics include paclitaxel, (e.g., TAXOL® by Bristol-Myers Squibb Co., Stamford, Conn.), docetaxel (e.g., Taxotere®, from Aventis S.A., Frankfurt, Germany), methotrexate, azathioprine, vincristine, vinblastine, fluorouracil, doxorubicin hydrochloride (e.g., Adriamycin® from Pharmacia & Upjohn, Peapack N. J.), and mitomycin (e.g., Mutamycin® from Bristol-Myers Squibb Co., Stamford, Conn.). Examples of such antiplatelets, anticoagulants, antifibrin, and antithrombins include aspirin, sodium heparin, low molecular weight heparins, heparinoids, hirudin, argatroban, forskolin, vapiprost, prostacyclin and prostacyclin analogues, dextran, D-phe-pro-arg-chloromethylketone (synthetic antithrombin),
dipyridamole, glycoprotein Ilb/IIIa platelet membrane receptor antagonist antibody, recombinant hirudin, and thrombin inhibitors such as Angiomax a (Biogen, Inc., Cambridge, Mass.). Examples of such cytostatic or antiproliferative agents include angiopeptin, angiotensin converting enzyme inhibitors such as captopril (e.g., Capoten® and Capozide® from Bristol-Myers Squibb Co., Stamford, Conn.), cilazapril or lisinopril (e.g., Prinivil® and Prinzide® from Merck & Co., Inc., Whitehouse Station, NJ), calcium channel blockers (such as nifedipine), colchicine, proteins, peptides, fibroblast growth factor (FGF) antagonists, fish oil (omega 3 -fatty acid), histamine antagonists, lovastatin (an inhibitor of HMG-CoA reductase, a cholesterol lowering drug, brand name Mevacor® from Merck & Co., Inc., Whitehouse Station, NJ), monoclonal antibodies (such as those specific for Platelet-Derived Growth Factor (PDGF) receptors), nitroprusside, phosphodiesterase inhibitors, prostaglandin inhibitors, suramin, serotonin blockers, steroids, thioprotease inhibitors, triazolopyrimidine (a PDGF antagonist), and nitric oxide. An example of an antiallergic agent is permirolast potassium. Other therapeutic substances or agents which may be appropriate agents include cisplatin, insulin sensitizers, receptor tyrosine kinase inhibitors, carboplatin, alpha-interferon, genetically engineered epithelial cells, steroidal anti-inflammatory agents, non-steroidal antiinflammatory agents, antivirals, anticancer drugs, anticoagulant agents, free radical scavengers, estradiol, antibiotics, nitric oxide donors, super oxide dismutases, super oxide dismutases mimics, 4-amino-2,2,6,6-tetramethylpiperidine-l-oxyl (4-amino-TEMPO), tacrolimus, dexamethasone, ABT-578, clobetasol, cytostatic agents, prodrugs thereof, co- drugs thereof, and a combination thereof. Other therapeutic substances or agents may include rapamycin and structural derivatives or functional analogs thereof, such as 40-O- (2-hydroxy)ethyl-raρamycin (everolimus), 40-O-(3-hydroxy)propyl-rapamycin, 40-O-[2- (2-hydroxy)ethoxy]ethyl-rapamycin, and 40-O-tetrazole-rapaniycin.
FIG. 4 is a diagram illustrating a front view of the end wall 23 of the support
member 22 (which can be similar to the end wall 27 of the lock member 26) of the stent
mandrel fixture 20 (FIG. 2). The plurality of elements, support arms or wires 36 includes
3 wires spaced 120° apart from each other. The plurality of wires 36 extend from the circumference of the support member 22 to the bore 38. In other embodiments, the
plurality of wires 36 can be spaced apart differently and/or comprise a different number
of wires 36.
FIG. 5 is a diagram illustrating a perspective view of the support member 22
(which can be similar to that of the lock member 26). In an embodiment of the invention,
the plurality of wires 36 may have pointed ends such that the sections of the ends facing the mandrel 24 run parallel with the mandrel 24, which enables a smoother fit between
the mandrel 24 and the wires 36.
FIG. 6 is a diagram illustrating the stent 10 mounted on the stent mandrel fixture
20. When the stent 10 is mounted, the elements, support arms or wires 36 and 42 contact the mandrel and the stent 10 is supported by the wires 36 as well as the wires 42. As
such, the stent 10 only interfaces with the stent mandrel fixture 20 at six minute points,
thereby limiting the area at which clumps can form. Further, the support member 22 can
include a lock pin 65 that extends from a surface of the member 22 through to the
mandrel 24 for locking the mandrel in place. FIG. 7 is a diagram illustrating a support member 22 and a locking member 26
according to another embodiment of the invention. The support member 22 and the
locking member 26 each have two wires extending there from. When the stent 10 is
mounted to the members 22 and 26, one of the members is rotated 90° with respect to the other to ensure that the stent 10 is adequately supported, as is shown.
FIG. 8 and FIG. 9 are diagrams illustrating a support member 22 according to another embodiment of the invention. The support member 22 of FIG. 8 and FIG. 9 has a plurality of elements, support arms or wires (e.g., 3) 52 extending laterally from the support member 22. The elements can extend parallel to the longitudinal axis of a stent or parallel to the longitudinal axis of the mandrel 24. The elements, support arms or wires 52 may be about 4 to about 8 mm in length and about 0.004 to about 0.008 inches in diameter. The elements, support arms or wires 52 each have a sphere 54 at their respective ends. In some embodiment, the spheres 54 are large enough so as to prevent the inner side of a stent from making contact with the element 52. In one embodiment, the size of the spheres 54 should be larger than a gap between the struts under which the spheres are placed and small enough so that no portion of the spheres 52 protrudes out of the outer surface of the stent. In some embodiments, a portion of the spheres can protrude out from the outer surface of the stent. By way of example, the spheres 54 can each have a diameter of about 0.015 to about 0.020 of an inch. The spheres 54 provide more rigid support than the wires 36 or 42 but provide more contact surface for a coating composition to pool, thereby slightly increasing the possibility of coating defects but still providing less surface area than conventional stent mounting fixtures.
In some embodiments, elements 36, 42 and/or 52 can extend starting from an inner position of the end wall of the support member 22 or lock member 26 to the edge of the end wall. In essence, this would be the opposite of the embodiment illustrated by FIG. 3. In this embodiment, the elements would be extending or branching outward, away from one another. The use of the mandrel 24 in this embodiment, as well as the other embodiments described above, can certainly be optional, although preferred as a second motor may be required to be coupled to the lock member 26.
FIG. 10 is a flowchart illustrating a method 1000 of coating a stent. First a stent 10 is mounted (1010) on the stent mandrel fixture 20. Mounting (1010) can include rotating the support member 22 vertically, inserting the mandrel 24 into the bore 38, mounting the stent 10 on the wires 36 or 52, and repeating for the lock member 26. A high magnification video device can also be used during the mounting (1010) to assist in . adjusting the contact position between the wires 36 or 52 and the stent 10. The stent 10 is then rotated and/or translated (1020) and a coating is sprayed (1030) on the stent 10 during the rotation (1020). The rotation ratio of the mandrel and stent is 1:1 considering how elements 36 and 42 engage and rotate the stent. Air or gas can be applied (1040) to the stent for drying during and/or subsequent to the application of the coating composition. Acts of spraying and blowing can be repeated if desired (1050). The method 1000 then ends.
FIG. 11 is a diagram illustrating a stent 10 coated using the stent mandrel fixture 20. As can be seen, there are no defects, such as inner diameter tearing, rough surfaces, cob webs, etc., at the end of the stent 10.
The foregoing description of the illustrated embodiments of the present invention is by way of example only, and other variations and modifications of the above-described embodiments and methods are possible in light of the foregoing teaching. For example, the plurality of wires 52 may also be coated with a non-stick polymeric material having less adhesive force with the coating substance than with the members.
Claims
1. A stent fixture for supporting a stent during formation of a coating, comprising a structure having arm elements extending from the structure, the arm elements are configured to allow an inner side of a stent to rest on and be supported by the arm elements.
2. The fixture of claim 1, wherein the structure supports one end of the stent and wherein the fixture additionally comprises a second structure for support an opposing end of the stent.
3. The fixture of claim 2, wherein the second structure comprises arm elements extending out from the second structure, the arm elements of the second structure are configured to allow the inner side of the stent to rest on and be supported by the arm elements of the second structure.
4. The fixture of claim 3, additionally comprising a third structure connecting the structure to the second structure and extending through a longitudinal bore of the stent, wherein the stent can be securely pinched between the plurality of arm elements of the structures.
5. The fixture of claim 3, wherein the arm elements are slanted away from the inner side of the stent.
6. The fixture of claim 3, wherein the arm elements are parallel to a longitudinal axis of the stent.
7. The fixture of claim 3, wherein the arm elements include spheres positioned at an end of the aπn elements.
8. The fixture of claim 1, wherein the arm elements are slanted away from the inner side of the stent.
9. The fixture of claim 1, wherein the structure includes an end wall facing the stent and wherein the arm elements extend out from the end wall of the structure.
10. The fixture of claim 9, wherein the arm elements extend out from a perimeter position on the end wall and converge towards each other towards a middle section of the end wall.
11. The fixture of claim 1, wherein the arm elements include spheres positioned at an end thereof.
12. The fixture of claim 11 , wherein the spheres make contact with the inner side of the stent.
13. The fixture of claim 1, wherein the arm elements are of a suitable size so as to be able to penetrate at least partially into an open crown of struts of the stent.
14. The fixture of claim 1, wherein the arm elements are of suitable size so as to be able to be inserted at least partially in a space between two struts of the stent or a space between two section of a strut of the stent.
15. The fixture of claim 1, wherein the arm elements angularly extend out from the structure such that when an end of the stent is placed over the arm elements, the arm elements prevent the structure from making contact with the stent.
16. The fixture of claim 1, wherein the arm elements are positioned about the perimeter of the structure and do not contact one another.
17. The fixture of claim 1, additionally comprising a mandrel for extending out from the structure and configured to extend at least partially into a longitudinal bore of the stent.
18. The fixture of claim 17, wherein the arm elements prevent the mandrel from making contact with the inner side of the stent during formation of the coating.
19. The fixture of claim 17, wherein the arm elements converge at an angle towards the mandrel but do not make contact with the mandrel.
20. The fixture of claim 17, wherein the arm elements converge at an angle towards the mandrel and make contact with the mandrel.
21. A method of coating a stent with a substance, comprising: positioning the stent on the fixture of claim 1 and applying a coating substance to the stent.
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US11/174,195 US7823533B2 (en) | 2005-06-30 | 2005-06-30 | Stent fixture and method for reducing coating defects |
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Families Citing this family (20)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7823533B2 (en) * | 2005-06-30 | 2010-11-02 | Advanced Cardiovascular Systems, Inc. | Stent fixture and method for reducing coating defects |
US7735449B1 (en) * | 2005-07-28 | 2010-06-15 | Advanced Cardiovascular Systems, Inc. | Stent fixture having rounded support structures and method for use thereof |
US7833261B2 (en) * | 2005-12-12 | 2010-11-16 | Advanced Cardiovascular Systems, Inc. | Severable support for a stent |
US8069814B2 (en) | 2006-05-04 | 2011-12-06 | Advanced Cardiovascular Systems, Inc. | Stent support devices |
US8003157B2 (en) * | 2007-06-15 | 2011-08-23 | Abbott Cardiovascular Systems Inc. | System and method for coating a stent |
US7812941B2 (en) * | 2007-06-15 | 2010-10-12 | Abbott Cardiovascular Systems Inc. | Systems and methods for the inspection of cylinders |
US8367150B2 (en) | 2007-06-15 | 2013-02-05 | Abbott Cardiovascular Systems Inc. | Methods and apparatus for coating stents |
US8677650B2 (en) * | 2007-06-15 | 2014-03-25 | Abbott Cardiovascular Systems Inc. | Methods and devices for drying coated stents |
US7897195B2 (en) * | 2007-06-15 | 2011-03-01 | Abbott Cardiovascular Systems Inc. | Devices for coating stents |
US7885788B2 (en) | 2007-06-15 | 2011-02-08 | Abbott Cardiovascular Systems Inc. | Method and apparatus for weighing a stent |
US7606625B2 (en) * | 2007-06-15 | 2009-10-20 | Abbott Cardiovascular Systems Inc. | Method and device for aligning a stent with a stent support |
US8689728B2 (en) * | 2007-10-05 | 2014-04-08 | Menendez Adolfo | Apparatus for holding a medical device during coating |
US8567340B2 (en) | 2009-08-12 | 2013-10-29 | Abbott Cardiovascular Systems Inc. | System and method for coating a medical device |
US20130035753A1 (en) * | 2011-08-01 | 2013-02-07 | Abbott Cardiovascular Systems Inc. | Multiple Scaffold Design And Coating Thereof |
US9320592B2 (en) | 2013-03-15 | 2016-04-26 | Covidien Lp | Coated medical devices and methods of making and using same |
US9545301B2 (en) | 2013-03-15 | 2017-01-17 | Covidien Lp | Coated medical devices and methods of making and using same |
US9668890B2 (en) | 2013-11-22 | 2017-06-06 | Covidien Lp | Anti-thrombogenic medical devices and methods |
US9789228B2 (en) | 2014-12-11 | 2017-10-17 | Covidien Lp | Antimicrobial coatings for medical devices and processes for preparing such coatings |
CN105665195B (en) * | 2016-03-23 | 2017-12-26 | 张立栋 | A kind of cylindrical ceramic product clamping device with heater |
CN108126846A (en) * | 2016-03-23 | 2018-06-08 | 长沙德科投资管理咨询有限公司 | A kind of Horizontal cylinder shape ceramic product clamping device |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6527863B1 (en) * | 2001-06-29 | 2003-03-04 | Advanced Cardiovascular Systems, Inc. | Support device for a stent and a method of using the same to coat a stent |
US6673154B1 (en) * | 2001-06-28 | 2004-01-06 | Advanced Cardiovascular Systems, Inc. | Stent mounting device to coat a stent |
WO2004008995A2 (en) * | 2002-07-19 | 2004-01-29 | Boston Scientific Limited | Stent coating holders |
Family Cites Families (414)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US666034A (en) * | 1900-05-18 | 1901-01-15 | Morris Solomon | Lap-robe. |
FR732895A (en) | 1932-10-18 | 1932-09-25 | Consortium Elektrochem Ind | Articles spun in polyvinyl alcohol |
US2386454A (en) | 1940-11-22 | 1945-10-09 | Bell Telephone Labor Inc | High molecular weight linear polyester-amides |
US2845346A (en) | 1954-01-13 | 1958-07-29 | Schwarzkopf Dev Co | Method of forming porous cemented metal powder bodies |
US3016875A (en) | 1958-12-11 | 1962-01-16 | United States Steel Corp | Apparatus for coating pipe |
US3849514A (en) | 1967-11-17 | 1974-11-19 | Eastman Kodak Co | Block polyester-polyamide copolymers |
US3773737A (en) | 1971-06-09 | 1973-11-20 | Sutures Inc | Hydrolyzable polymers of amino acid and hydroxy acids |
BE793124A (en) | 1972-06-23 | 1973-04-16 | Wheeling Pittsburgh Steel Corp | METAL PROTECTIVE TUBES FOR ELECTRICAL PIPES |
US3882816A (en) | 1972-09-22 | 1975-05-13 | Western Electric Co | Apparatus for forming layers of fusible metal on articles |
US3995075A (en) | 1974-04-18 | 1976-11-30 | Continental Can Company, Inc. | Inside stripe by intermittent exterior spray guns |
US4011388A (en) | 1974-07-02 | 1977-03-08 | E. I. Du Pont De Nemours And Company | Process for preparing emulsions by polymerization of aqueous monomer-polymer dispersions |
US4201149A (en) | 1974-12-17 | 1980-05-06 | Basf Aktiengesellschaft | Apparatus for spin coating in the production of thin magnetic layers for magnetic discs |
US4374669A (en) | 1975-05-09 | 1983-02-22 | Mac Gregor David C | Cardiovascular prosthetic devices and implants with porous systems |
US4082212A (en) | 1976-03-15 | 1978-04-04 | Southwire Company | Galvanized tube welded seam repair metallizing process |
DE2935097A1 (en) | 1978-09-07 | 1980-03-20 | Kuraray Co | AETHYLENE / VINYL ALCOHOL COPOLYMER MEMBRANE |
US4329383A (en) | 1979-07-24 | 1982-05-11 | Nippon Zeon Co., Ltd. | Non-thrombogenic material comprising substrate which has been reacted with heparin |
US4226243A (en) | 1979-07-27 | 1980-10-07 | Ethicon, Inc. | Surgical devices of polyesteramides derived from bis-oxamidodiols and dicarboxylic acids |
SU790725A1 (en) | 1979-07-27 | 1983-01-23 | Ордена Ленина Институт Элементоорганических Соединений Ан Ссср | Process for preparing alkylaromatic polyimides |
US4290383A (en) | 1979-07-31 | 1981-09-22 | Creative Craftsmen, Inc. | Spraying arrangement |
SU872531A1 (en) | 1979-08-07 | 1981-10-15 | Институт Физиологии Им.И.С.Бериташвили Ан Гсср | Method of producing polyurethans |
SU811750A1 (en) | 1979-08-07 | 1983-09-23 | Институт Физиологии Им.С.И.Бериташвили | Bis-bicarbonates of aliphatic diols as monomers for preparing polyurethanes and process for producing the same |
SU876663A1 (en) | 1979-11-11 | 1981-10-30 | Институт Физиологии Им. Академика И.С.Бериташвили Ан Гсср | Method of producing polyarylates |
SU1016314A1 (en) | 1979-12-17 | 1983-05-07 | Институт Физиологии Им.И.С.Бериташвили | Process for producing polyester urethanes |
US4343931A (en) | 1979-12-17 | 1982-08-10 | Minnesota Mining And Manufacturing Company | Synthetic absorbable surgical devices of poly(esteramides) |
US4529792A (en) | 1979-12-17 | 1985-07-16 | Minnesota Mining And Manufacturing Company | Process for preparing synthetic absorbable poly(esteramides) |
SU905228A1 (en) | 1980-03-06 | 1982-02-15 | Институт Физиологии Им. Акад.И.С. Бериташвили Ан Гсср | Method for preparing thiourea |
US4629563B1 (en) | 1980-03-14 | 1997-06-03 | Memtec North America | Asymmetric membranes |
US4489670A (en) | 1983-05-16 | 1984-12-25 | Sermetel | Fixture for centrifugal apparatus |
US4560374A (en) | 1983-10-17 | 1985-12-24 | Hammerslag Julius G | Method for repairing stenotic vessels |
JPS6174668A (en) | 1984-09-19 | 1986-04-16 | Yoshida Kogyo Kk <Ykk> | Device for supplying separate paint in rotary painting machine |
US4640846A (en) | 1984-09-25 | 1987-02-03 | Yue Kuo | Semiconductor spin coating method |
SU1293518A1 (en) | 1985-04-11 | 1987-02-28 | Тбилисский зональный научно-исследовательский и проектный институт типового и экспериментального проектирования жилых и общественных зданий | Installation for testing specimen of cross-shaped structure |
JPS61276561A (en) | 1985-05-31 | 1986-12-06 | 株式会社クラレ | Blood treatment apparatus |
US4656242A (en) | 1985-06-07 | 1987-04-07 | Henkel Corporation | Poly(ester-amide) compositions |
SE459005B (en) | 1985-07-12 | 1989-05-29 | Aake Rikard Lindahl | SET TO MANUFACTURE SPHERICAL POLYMER PARTICLES |
US4733665C2 (en) | 1985-11-07 | 2002-01-29 | Expandable Grafts Partnership | Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft |
US4611051A (en) | 1985-12-31 | 1986-09-09 | Union Camp Corporation | Novel poly(ester-amide) hot-melt adhesives |
JPS6346171A (en) | 1986-06-06 | 1988-02-27 | 旭光学工業株式会社 | Support of medical device stayed in living body |
US4882168A (en) | 1986-09-05 | 1989-11-21 | American Cyanamid Company | Polyesters containing alkylene oxide blocks as drug delivery systems |
US5017420A (en) | 1986-10-23 | 1991-05-21 | Hoechst Celanese Corp. | Process for preparing electrically conductive shaped articles from polybenzimidazoles |
JPH0696023B2 (en) | 1986-11-10 | 1994-11-30 | 宇部日東化成株式会社 | Artificial blood vessel and method for producing the same |
US4893623A (en) | 1986-12-09 | 1990-01-16 | Advanced Surgical Intervention, Inc. | Method and apparatus for treating hypertrophy of the prostate gland |
US4762128A (en) | 1986-12-09 | 1988-08-09 | Advanced Surgical Intervention, Inc. | Method and apparatus for treating hypertrophy of the prostate gland |
IT1196836B (en) | 1986-12-12 | 1988-11-25 | Sorin Biomedica Spa | Polymeric or metal alloy prosthesis with biocompatible carbon coating |
US5721131A (en) | 1987-03-06 | 1998-02-24 | United States Of America As Represented By The Secretary Of The Navy | Surface modification of polymers with self-assembled monolayers that promote adhesion, outgrowth and differentiation of biological cells |
US4800882A (en) | 1987-03-13 | 1989-01-31 | Cook Incorporated | Endovascular stent and delivery system |
JPS63238872A (en) | 1987-03-25 | 1988-10-04 | テルモ株式会社 | Instrument for securing inner diameter of cavity of tubular organ and catheter equipped therewith |
US6387379B1 (en) | 1987-04-10 | 2002-05-14 | University Of Florida | Biofunctional surface modified ocular implants, surgical instruments, medical devices, prostheses, contact lenses and the like |
US5527337A (en) | 1987-06-25 | 1996-06-18 | Duke University | Bioabsorbable stent and method of making the same |
US5059211A (en) | 1987-06-25 | 1991-10-22 | Duke University | Absorbable vascular stent |
US4894231A (en) | 1987-07-28 | 1990-01-16 | Biomeasure, Inc. | Therapeutic agent delivery system |
US4886062A (en) | 1987-10-19 | 1989-12-12 | Medtronic, Inc. | Intravascular radially expandable stent and method of implant |
US4906423A (en) | 1987-10-23 | 1990-03-06 | Dow Corning Wright | Methods for forming porous-surfaced polymeric bodies |
US5019096A (en) | 1988-02-11 | 1991-05-28 | Trustees Of Columbia University In The City Of New York | Infection-resistant compositions, medical devices and surfaces and methods for preparing and using same |
JP2561309B2 (en) | 1988-03-28 | 1996-12-04 | テルモ株式会社 | Medical material and manufacturing method thereof |
US4865879A (en) | 1988-03-31 | 1989-09-12 | Gordon Finlay | Method for restoring and reinforcing wooden structural component |
US4931287A (en) | 1988-06-14 | 1990-06-05 | University Of Utah | Heterogeneous interpenetrating polymer networks for the controlled release of drugs |
US5328471A (en) | 1990-02-26 | 1994-07-12 | Endoluminal Therapeutics, Inc. | Method and apparatus for treatment of focal disease in hollow tubular organs and other tissue lumens |
US4846791A (en) | 1988-09-02 | 1989-07-11 | Advanced Medical Technology & Development Corp. | Multi-lumen catheter |
US4977901A (en) | 1988-11-23 | 1990-12-18 | Minnesota Mining And Manufacturing Company | Article having non-crosslinked crystallized polymer coatings |
US5584433A (en) | 1991-08-22 | 1996-12-17 | Nakagawa; Mitsuyoshi | Atomization method and atomizer |
US5201314A (en) | 1989-03-09 | 1993-04-13 | Vance Products Incorporated | Echogenic devices, material and method |
US4992312A (en) | 1989-03-13 | 1991-02-12 | Dow Corning Wright Corporation | Methods of forming permeation-resistant, silicone elastomer-containing composite laminates and devices produced thereby |
JP3133750B2 (en) | 1989-03-24 | 2001-02-13 | キヤノン株式会社 | Ink jet cartridge and ink jet recording apparatus using the same |
US4976736A (en) | 1989-04-28 | 1990-12-11 | Interpore International | Coated biomaterials and methods for making same |
JPH0666255B2 (en) | 1989-05-02 | 1994-08-24 | 三菱電機株式会社 | Spin coating apparatus and method |
US5264246A (en) | 1989-05-02 | 1993-11-23 | Mitsubishi Denki Kabushiki Kaisha | Spin coating method |
IL90193A (en) | 1989-05-04 | 1993-02-21 | Biomedical Polymers Int | Polurethane-based polymeric materials and biomedical articles and pharmaceutical compositions utilizing the same |
US4955899A (en) | 1989-05-26 | 1990-09-11 | Impra, Inc. | Longitudinally compliant vascular graft |
US5037392A (en) | 1989-06-06 | 1991-08-06 | Cordis Corporation | Stent-implanting balloon assembly |
US5272012A (en) | 1989-06-23 | 1993-12-21 | C. R. Bard, Inc. | Medical apparatus having protective, lubricious coating |
JP3031924B2 (en) | 1989-07-07 | 2000-04-10 | フロイント産業株式会社 | Granulation coating equipment |
US5458683A (en) | 1989-07-17 | 1995-10-17 | Crc-Evans Rehabilitation Systems, Inc. | Device for surface cleaning, surface preparation and coating applications |
US5971954A (en) | 1990-01-10 | 1999-10-26 | Rochester Medical Corporation | Method of making catheter |
EP0514406B1 (en) | 1990-01-30 | 1994-03-02 | Akzo Nobel N.V. | Article for the controlled delivery of an active substance, comprising a hollow space fully enclosed by a wall and filled in full or in part with one or more active substances |
US5242399A (en) | 1990-04-25 | 1993-09-07 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5306501A (en) | 1990-05-01 | 1994-04-26 | Mediventures, Inc. | Drug delivery by injection with thermoreversible gels containing polyoxyalkylene copolymers |
US5292516A (en) | 1990-05-01 | 1994-03-08 | Mediventures, Inc. | Body cavity drug delivery with thermoreversible gels containing polyoxyalkylene copolymers |
US5300295A (en) | 1990-05-01 | 1994-04-05 | Mediventures, Inc. | Ophthalmic drug delivery with thermoreversible polyoxyalkylene gels adjustable for pH |
US5298260A (en) | 1990-05-01 | 1994-03-29 | Mediventures, Inc. | Topical drug delivery with polyoxyalkylene polymer thermoreversible gels adjustable for pH and osmolality |
WO1991017724A1 (en) | 1990-05-17 | 1991-11-28 | Harbor Medical Devices, Inc. | Medical device polymer |
CA2038605C (en) | 1990-06-15 | 2000-06-27 | Leonard Pinchuk | Crack-resistant polycarbonate urethane polymer prostheses and the like |
US6060451A (en) | 1990-06-15 | 2000-05-09 | The National Research Council Of Canada | Thrombin inhibitors based on the amino acid sequence of hirudin |
CA2081896A1 (en) | 1990-06-15 | 1991-12-16 | James E. Shapland | Drug delivery apparatus and method |
US5112457A (en) | 1990-07-23 | 1992-05-12 | Case Western Reserve University | Process for producing hydroxylated plasma-polymerized films and the use of the films for enhancing the compatiblity of biomedical implants |
US5455040A (en) | 1990-07-26 | 1995-10-03 | Case Western Reserve University | Anticoagulant plasma polymer-modified substrate |
US5163952A (en) | 1990-09-14 | 1992-11-17 | Michael Froix | 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 |
US6248129B1 (en) | 1990-09-14 | 2001-06-19 | Quanam Medical Corporation | Expandable polymeric stent with memory and delivery apparatus and method |
US5462990A (en) | 1990-10-15 | 1995-10-31 | Board Of Regents, The University Of Texas System | Multifunctional organic polymers |
GB9027793D0 (en) | 1990-12-21 | 1991-02-13 | Ucb Sa | Polyester-amides containing terminal carboxyl groups |
US5171445A (en) | 1991-03-26 | 1992-12-15 | Memtec America Corporation | Ultraporous and microporous membranes and method of making membranes |
US5188734A (en) | 1991-03-26 | 1993-02-23 | Memtec America Corporation | Ultraporous and microporous integral membranes |
US5330768A (en) | 1991-07-05 | 1994-07-19 | Massachusetts Institute Of Technology | Controlled drug delivery using polymer/pluronic blends |
WO1993004720A1 (en) | 1991-09-12 | 1993-03-18 | THE UNITED STATES, as represented by SECRETARY DEPARTMENT OF HEALTH AND HUMAN SERVICES | Apparatus for and method of making ultra thin walled wire reinforced endotracheal tubing and product thereof |
US5229045A (en) | 1991-09-18 | 1993-07-20 | Kontron Instruments Inc. | Process for making porous membranes |
US5500013A (en) | 1991-10-04 | 1996-03-19 | Scimed Life Systems, Inc. | Biodegradable drug delivery vascular stent |
US5234457A (en) | 1991-10-09 | 1993-08-10 | Boston Scientific Corporation | Impregnated stent |
CA2380683C (en) | 1991-10-28 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Expandable stents and method for making same |
US5573934A (en) | 1992-04-20 | 1996-11-12 | Board Of Regents, The University Of Texas System | Gels for encapsulation of biological materials |
US5599352A (en) | 1992-03-19 | 1997-02-04 | Medtronic, Inc. | Method of making a drug eluting stent |
US5282823A (en) | 1992-03-19 | 1994-02-01 | Medtronic, Inc. | Intravascular radially expandable stent |
GB9206736D0 (en) | 1992-03-27 | 1992-05-13 | Sandoz Ltd | Improvements of organic compounds and their use in pharmaceutical compositions |
US5219980A (en) | 1992-04-16 | 1993-06-15 | Sri International | Polymers biodegradable or bioerodiable into amino acids |
EP0568451B1 (en) | 1992-04-28 | 1999-08-04 | Terumo Kabushiki Kaisha | Thermoplastic polymer composition and medical devices made of the same |
DE4220295A1 (en) * | 1992-06-20 | 1993-12-23 | Angiomed Ag | Device for correcting the position of a stent |
US5358740A (en) | 1992-06-24 | 1994-10-25 | Massachusetts Institute Of Technology | Method for low pressure spin coating and low pressure spin coating apparatus |
DE4224401A1 (en) | 1992-07-21 | 1994-01-27 | Pharmatech Gmbh | New biodegradable homo- and co-polymer(s) for pharmaceutical use - produced by polycondensation of prod. from heterolytic cleavage of aliphatic polyester with functionalised (cyclo)aliphatic cpd. |
US5342621A (en) | 1992-09-15 | 1994-08-30 | Advanced Cardiovascular Systems, Inc. | Antithrombogenic surface |
FR2699168B1 (en) | 1992-12-11 | 1995-01-13 | Rhone Poulenc Chimie | Method of treating a material comprising a polymer by hydrolysis. |
DE4242476C1 (en) | 1992-12-16 | 1994-08-11 | Eppendorf Geraetebau Netheler | Device for centrifuging samples |
EP0604022A1 (en) | 1992-12-22 | 1994-06-29 | Advanced Cardiovascular Systems, Inc. | Multilayered biodegradable stent and method for its manufacture |
WO1994021320A1 (en) | 1993-03-15 | 1994-09-29 | Advanced Cardiovascular Systems, Inc. | Fluid delivery catheter |
US5378511A (en) | 1993-03-22 | 1995-01-03 | International Business Machines Corporation | Material-saving resist spinner and process |
US5308338A (en) | 1993-04-22 | 1994-05-03 | Helfrich G Baird | Catheter or the like with medication injector to prevent infection |
US5824048A (en) | 1993-04-26 | 1998-10-20 | Medtronic, Inc. | Method for delivering a therapeutic substance to a body lumen |
US5464650A (en) | 1993-04-26 | 1995-11-07 | Medtronic, Inc. | Intravascular stent and method |
US20020055710A1 (en) | 1998-04-30 | 2002-05-09 | Ronald J. Tuch | Medical device for delivering a therapeutic agent and method of preparation |
IT1276342B1 (en) | 1993-06-04 | 1997-10-30 | Ist Naz Stud Cura Dei Tumori | METAL STENT COVERED WITH BIOCOMPATIBLE POLYMERIC MATERIAL |
JPH0767895A (en) | 1993-06-25 | 1995-03-14 | Sumitomo Electric Ind Ltd | Antimicrobial artificial blood vessel and suture yarn for antimicrobial operation |
US5994341A (en) | 1993-07-19 | 1999-11-30 | Angiogenesis Technologies, Inc. | Anti-angiogenic Compositions and methods for the treatment of arthritis |
EG20321A (en) | 1993-07-21 | 1998-10-31 | Otsuka Pharma Co Ltd | Medical material and process for producing the same |
DE4327024A1 (en) | 1993-08-12 | 1995-02-16 | Bayer Ag | Thermoplastically processable and biodegradable aliphatic polyesteramides |
US5380299A (en) | 1993-08-30 | 1995-01-10 | Med Institute, Inc. | Thrombolytic treated intravascular medical device |
US5578048A (en) | 1993-09-15 | 1996-11-26 | United States Surgical Corporation | Manipulator apparatus |
WO1995010989A1 (en) | 1993-10-19 | 1995-04-27 | Scimed Life Systems, Inc. | Intravascular stent pump |
US5723004A (en) | 1993-10-21 | 1998-03-03 | Corvita Corporation | Expandable supportive endoluminal grafts |
US5855598A (en) | 1993-10-21 | 1999-01-05 | Corvita Corporation | Expandable supportive branched endoluminal grafts |
JP3758048B2 (en) | 1993-10-26 | 2006-03-22 | 帝国ピストンリング株式会社 | Ring coating method and coating device |
JP2703510B2 (en) | 1993-12-28 | 1998-01-26 | アドヴァンスド カーディオヴァスキュラー システムズ インコーポレーテッド | Expandable stent and method of manufacturing the same |
US5759205A (en) | 1994-01-21 | 1998-06-02 | Brown University Research Foundation | Negatively charged polymeric electret implant |
US6051576A (en) | 1994-01-28 | 2000-04-18 | University Of Kentucky Research Foundation | Means to achieve sustained release of synergistic drugs by conjugation |
CA2190121A1 (en) | 1994-03-15 | 1995-09-21 | Edith Mathiowitz | Polymeric gene delivery system |
US5656082A (en) | 1994-04-04 | 1997-08-12 | Tatsumo Kabushiki Kaisha | Liquid applying apparatus utilizing centrifugal force |
US5567410A (en) | 1994-06-24 | 1996-10-22 | The General Hospital Corporation | Composotions and methods for radiographic imaging |
US5629077A (en) | 1994-06-27 | 1997-05-13 | Advanced Cardiovascular Systems, Inc. | Biodegradable mesh and film stent |
US5670558A (en) | 1994-07-07 | 1997-09-23 | Terumo Kabushiki Kaisha | Medical instruments that exhibit surface lubricity when wetted |
US5788979A (en) | 1994-07-22 | 1998-08-04 | Inflow Dynamics Inc. | Biodegradable coating with inhibitory properties for application to biocompatible materials |
US5516881A (en) | 1994-08-10 | 1996-05-14 | Cornell Research Foundation, Inc. | Aminoxyl-containing radical spin labeling in polymers and copolymers |
US5891108A (en) | 1994-09-12 | 1999-04-06 | Cordis Corporation | Drug delivery stent |
US5578073A (en) | 1994-09-16 | 1996-11-26 | Ramot Of Tel Aviv University | Thromboresistant surface treatment for biomaterials |
US5649977A (en) | 1994-09-22 | 1997-07-22 | Advanced Cardiovascular Systems, Inc. | Metal reinforced polymer stent |
US5558900A (en) | 1994-09-22 | 1996-09-24 | Fan; You-Ling | One-step thromboresistant, lubricious coating |
US5485496A (en) | 1994-09-22 | 1996-01-16 | Cornell Research Foundation, Inc. | Gamma irradiation sterilizing of biomaterial medical devices or products, with improved degradation and mechanical properties |
FR2724938A1 (en) | 1994-09-28 | 1996-03-29 | Lvmh Rech | POLYMERS FUNCTIONALIZED BY AMINO ACIDS OR AMINO ACID DERIVATIVES, THEIR USE AS SURFACTANTS, IN PARTICULAR, IN COSMETIC COMPOSITIONS AND IN PARTICULAR NAIL POLISH. |
ATE198979T1 (en) | 1994-10-12 | 2001-02-15 | Focal Inc | TARGETED DISHES ADMINISTERED USING BIODEGRADABLE POLYMERS |
US5643580A (en) | 1994-10-17 | 1997-07-01 | Surface Genesis, Inc. | Biocompatible coating, medical device using the same and methods |
US5836965A (en) | 1994-10-19 | 1998-11-17 | Jendersee; Brad | Stent delivery and deployment method |
US5707385A (en) | 1994-11-16 | 1998-01-13 | Advanced Cardiovascular Systems, Inc. | Drug loaded elastic membrane and method for delivery |
US5637113A (en) | 1994-12-13 | 1997-06-10 | Advanced Cardiovascular Systems, Inc. | Polymer film for wrapping a stent structure |
US5569198A (en) | 1995-01-23 | 1996-10-29 | Cortrak Medical Inc. | Microporous catheter |
US5919570A (en) | 1995-02-01 | 1999-07-06 | Schneider Inc. | Slippery, tenaciously adhering hydrogel coatings containing a polyurethane-urea polymer hydrogel commingled with a poly(N-vinylpyrrolidone) polymer hydrogel, coated polymer and metal substrate materials, and coated medical devices |
US6017577A (en) | 1995-02-01 | 2000-01-25 | Schneider (Usa) Inc. | Slippery, tenaciously adhering hydrophilic polyurethane hydrogel coatings, coated polymer substrate materials, and coated medical devices |
US5702754A (en) | 1995-02-22 | 1997-12-30 | Meadox Medicals, Inc. | Method of providing a substrate with a hydrophilic coating and substrates, particularly medical devices, provided with such coatings |
US5869127A (en) | 1995-02-22 | 1999-02-09 | Boston Scientific Corporation | Method of providing a substrate with a bio-active/biocompatible coating |
US6231600B1 (en) | 1995-02-22 | 2001-05-15 | Scimed Life Systems, Inc. | Stents with hybrid coating for medical devices |
US5854376A (en) | 1995-03-09 | 1998-12-29 | Sekisui Kaseihin Kogyo Kabushiki Kaisha | Aliphatic ester-amide copolymer resins |
US5605696A (en) | 1995-03-30 | 1997-02-25 | Advanced Cardiovascular Systems, Inc. | Drug loaded polymeric material and method of manufacture |
US5837313A (en) | 1995-04-19 | 1998-11-17 | Schneider (Usa) Inc | Drug release stent coating process |
US6099562A (en) | 1996-06-13 | 2000-08-08 | Schneider (Usa) Inc. | Drug coating with topcoat |
WO1996033233A1 (en) | 1995-04-19 | 1996-10-24 | Kazunori Kataoka | Heterotelechelic block copolymers and process for producing the same |
US20020091433A1 (en) | 1995-04-19 | 2002-07-11 | Ni Ding | Drug release coated stent |
US6120536A (en) | 1995-04-19 | 2000-09-19 | Schneider (Usa) Inc. | Medical devices with long term non-thrombogenic coatings |
US5628786A (en) | 1995-05-12 | 1997-05-13 | Impra, Inc. | Radially expandable vascular graft with resistance to longitudinal compression and method of making same |
US5674242A (en) | 1995-06-06 | 1997-10-07 | Quanam Medical Corporation | Endoprosthetic device with therapeutic compound |
AU716005B2 (en) | 1995-06-07 | 2000-02-17 | Cook Medical Technologies Llc | Implantable medical device |
US6129761A (en) | 1995-06-07 | 2000-10-10 | Reprogenesis, Inc. | Injectable hydrogel compositions |
US7611533B2 (en) | 1995-06-07 | 2009-11-03 | Cook Incorporated | Coated implantable medical device |
US6010530A (en) | 1995-06-07 | 2000-01-04 | Boston Scientific Technology, Inc. | Self-expanding endoluminal prosthesis |
US5820917A (en) | 1995-06-07 | 1998-10-13 | Medtronic, Inc. | Blood-contacting medical device and method |
US7550005B2 (en) | 1995-06-07 | 2009-06-23 | Cook Incorporated | Coated implantable medical device |
US5609629A (en) | 1995-06-07 | 1997-03-11 | Med Institute, Inc. | Coated implantable medical device |
US6774278B1 (en) | 1995-06-07 | 2004-08-10 | Cook Incorporated | Coated implantable medical device |
CH690857A5 (en) | 1995-07-04 | 2001-02-15 | Erich Bergmann | System for plasma-enhanced physical Hochvakuumbedampfung workpieces with wear-resistant coatings and methods for performing in this complex |
US5667767A (en) | 1995-07-27 | 1997-09-16 | Micro Therapeutics, Inc. | Compositions for use in embolizing blood vessels |
US5877224A (en) | 1995-07-28 | 1999-03-02 | Rutgers, The State University Of New Jersey | Polymeric drug formulations |
US5935135A (en) | 1995-09-29 | 1999-08-10 | United States Surgical Corporation | Balloon delivery system for deploying stents |
US5723219A (en) | 1995-12-19 | 1998-03-03 | Talison Research | Plasma deposited film networks |
US5607442A (en) | 1995-11-13 | 1997-03-04 | Isostent, Inc. | Stent with improved radiopacity and appearance characteristics |
US5788626A (en) | 1995-11-21 | 1998-08-04 | Schneider (Usa) Inc | Method of making a stent-graft covered with expanded polytetrafluoroethylene |
US5658995A (en) | 1995-11-27 | 1997-08-19 | Rutgers, The State University | Copolymers of tyrosine-based polycarbonate and poly(alkylene oxide) |
DE19545678A1 (en) | 1995-12-07 | 1997-06-12 | Goldschmidt Ag Th | Copolymers of polyamino acid esters |
JP4193917B2 (en) | 1995-12-18 | 2008-12-10 | アンジオデバイス インターナショナル ゲーエムベーハー | Crosslinked polymer composition and method of use thereof |
US6203569B1 (en) | 1996-01-04 | 2001-03-20 | Bandula Wijay | Flexible stent |
US6033582A (en) | 1996-01-22 | 2000-03-07 | Etex Corporation | Surface modification of medical implants |
US6054553A (en) | 1996-01-29 | 2000-04-25 | Bayer Ag | Process for the preparation of polymers having recurring agents |
US5772864A (en) | 1996-02-23 | 1998-06-30 | Meadox Medicals, Inc. | Method for manufacturing implantable medical devices |
US5823996A (en) | 1996-02-29 | 1998-10-20 | Cordis Corporation | Infusion balloon catheter |
CA2199890C (en) | 1996-03-26 | 2002-02-05 | Leonard Pinchuk | Stents and stent-grafts having enhanced hoop strength and methods of making the same |
US5713949A (en) | 1996-08-06 | 1998-02-03 | Jayaraman; Swaminathan | Microporous covered stents and method of coating |
US5932299A (en) | 1996-04-23 | 1999-08-03 | Katoot; Mohammad W. | Method for modifying the surface of an object |
US5955509A (en) | 1996-05-01 | 1999-09-21 | Board Of Regents, The University Of Texas System | pH dependent polymer micelles |
US5610241A (en) | 1996-05-07 | 1997-03-11 | Cornell Research Foundation, Inc. | Reactive graft polymer with biodegradable polymer backbone and method for preparing reactive biodegradable polymers |
US6440221B2 (en) | 1996-05-13 | 2002-08-27 | Applied Materials, Inc. | Process chamber having improved temperature control |
US6248398B1 (en) | 1996-05-22 | 2001-06-19 | Applied Materials, Inc. | Coater having a controllable pressurized process chamber for semiconductor processing |
US5876433A (en) | 1996-05-29 | 1999-03-02 | Ethicon, Inc. | Stent and method of varying amounts of heparin coated thereon to control treatment |
US5874165A (en) | 1996-06-03 | 1999-02-23 | Gore Enterprise Holdings, Inc. | Materials and method for the immobilization of bioactive species onto polymeric subtrates |
NL1003459C2 (en) | 1996-06-28 | 1998-01-07 | Univ Twente | Copoly (ester amides) and copoly (ester urethanes). |
US5928279A (en) | 1996-07-03 | 1999-07-27 | Baxter International Inc. | Stented, radially expandable, tubular PTFE grafts |
US5833659A (en) | 1996-07-10 | 1998-11-10 | Cordis Corporation | Infusion balloon catheter |
US5711958A (en) | 1996-07-11 | 1998-01-27 | Life Medical Sciences, Inc. | Methods for reducing or eliminating post-surgical adhesion formation |
US5741554A (en) | 1996-07-26 | 1998-04-21 | Bio Dot, Inc. | Method of dispensing a liquid reagent |
US5830178A (en) | 1996-10-11 | 1998-11-03 | Micro Therapeutics, Inc. | Methods for embolizing vascular sites with an emboilizing composition comprising dimethylsulfoxide |
US6060518A (en) | 1996-08-16 | 2000-05-09 | Supratek Pharma Inc. | Polymer compositions for chemotherapy and methods of treatment using the same |
US6174329B1 (en) | 1996-08-22 | 2001-01-16 | Advanced Cardiovascular Systems, Inc. | Protective coating for a stent with intermediate radiopaque coating |
US5980530A (en) | 1996-08-23 | 1999-11-09 | Scimed Life Systems Inc | Stent delivery system |
WO1998007523A1 (en) | 1996-08-23 | 1998-02-26 | Pursley Matt D | Apparatus and method for nonextrusion manufacturing of catheters |
US6306165B1 (en) | 1996-09-13 | 2001-10-23 | Meadox Medicals | ePTFE small caliber vascular grafts with significant patency enhancement via a surface coating which contains covalently bonded heparin |
US5911752A (en) | 1996-09-13 | 1999-06-15 | Intratherapeutics, Inc. | Method for collapsing a stent |
US5783657A (en) | 1996-10-18 | 1998-07-21 | Union Camp Corporation | Ester-terminated polyamides of polymerized fatty acids useful in formulating transparent gels in low polarity liquids |
US6244575B1 (en) | 1996-10-02 | 2001-06-12 | Micron Technology, Inc. | Method and apparatus for vaporizing liquid precursors and system for using same |
US6530951B1 (en) | 1996-10-24 | 2003-03-11 | Cook Incorporated | Silver implantable medical device |
US6197013B1 (en) | 1996-11-06 | 2001-03-06 | Setagon, Inc. | Method and apparatus for drug and gene delivery |
US6261320B1 (en) | 1996-11-21 | 2001-07-17 | Radiance Medical Systems, Inc. | Radioactive vascular liner |
ZA9710342B (en) | 1996-11-25 | 1998-06-10 | Alza Corp | Directional drug delivery stent and method of use. |
US6120491A (en) | 1997-11-07 | 2000-09-19 | The State University Rutgers | Biodegradable, anionic polymers derived from the amino acid L-tyrosine |
EP1014895B1 (en) | 1996-12-10 | 2006-03-08 | Purdue Research Foundation | Artificial vascular valves |
US6045899A (en) | 1996-12-12 | 2000-04-04 | Usf Filtration & Separations Group, Inc. | Highly assymetric, hydrophilic, microfiltration membranes having large pore diameters |
US5980972A (en) | 1996-12-20 | 1999-11-09 | Schneider (Usa) Inc | Method of applying drug-release coatings |
US5997517A (en) | 1997-01-27 | 1999-12-07 | Sts Biopolymers, Inc. | Bonding layers for medical device surface coatings |
AU5932198A (en) | 1997-01-28 | 1998-08-18 | United States Surgical Corporation | Polyesteramide, its preparation and surgical devices fabricated therefrom |
ES2192762T3 (en) | 1997-01-28 | 2003-10-16 | United States Surgical Corp | POLYESTERAMIDE, ITS PREPARATION AND SURGICAL DEVICES MANUFACTURED FROM IT. |
EP0960147B1 (en) | 1997-01-28 | 2004-09-29 | United States Surgical Corporation | Molded surgical device made from polyesteramides with amino acid-derived groups alternating with alpha-hydroxyacid-derived groups |
US6140431A (en) | 1997-02-27 | 2000-10-31 | Rohm And Haas Company | Process for preparing continuously variable-composition copolymers |
US6240616B1 (en) | 1997-04-15 | 2001-06-05 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing a medicated porous metal prosthesis |
US5843172A (en) | 1997-04-15 | 1998-12-01 | Advanced Cardiovascular Systems, Inc. | Porous medicated stent |
US6273913B1 (en) | 1997-04-18 | 2001-08-14 | Cordis Corporation | Modified stent useful for delivery of drugs along stent strut |
US5879697A (en) | 1997-04-30 | 1999-03-09 | Schneider Usa Inc | Drug-releasing coatings for medical devices |
US6159978A (en) | 1997-05-28 | 2000-12-12 | Aventis Pharmaceuticals Product, Inc. | Quinoline and quinoxaline compounds which inhibit platelet-derived growth factor and/or p56lck tyrosine kinases |
US6245760B1 (en) | 1997-05-28 | 2001-06-12 | Aventis Pharmaceuticals Products, Inc | Quinoline and quinoxaline compounds which inhibit platelet-derived growth factor and/or p56lck tyrosine kinases |
US6180632B1 (en) | 1997-05-28 | 2001-01-30 | Aventis Pharmaceuticals Products Inc. | Quinoline and quinoxaline compounds which inhibit platelet-derived growth factor and/or p56lck tyrosine kinases |
US6056993A (en) | 1997-05-30 | 2000-05-02 | Schneider (Usa) Inc. | Porous protheses and methods for making the same wherein the protheses are formed by spraying water soluble and water insoluble fibers onto a rotating mandrel |
US5902631A (en) | 1997-06-03 | 1999-05-11 | Wang; Lixiao | Lubricity gradient for medical devices |
FR2764794B1 (en) | 1997-06-20 | 1999-11-12 | Nycomed Lab Sa | EXPANDED TUBULAR DEVICE WITH VARIABLE THICKNESS |
US6110483A (en) | 1997-06-23 | 2000-08-29 | Sts Biopolymers, Inc. | Adherent, flexible hydrogel and medicated coatings |
US6194034B1 (en) | 1997-07-02 | 2001-02-27 | Konica Corporation | Method of coating a substrate wherein the flow rate of the coating solution is changed |
US6211249B1 (en) | 1997-07-11 | 2001-04-03 | Life Medical Sciences, Inc. | Polyester polyether block copolymers |
US5891507A (en) | 1997-07-28 | 1999-04-06 | Iowa-India Investments Company Limited | Process for coating a surface of a metallic stent |
US5980928A (en) | 1997-07-29 | 1999-11-09 | Terry; Paul B. | Implant for preventing conjunctivitis in cattle |
US5855600A (en) | 1997-08-01 | 1999-01-05 | Inflow Dynamics Inc. | Flexible implantable stent with composite design |
CN1273596A (en) | 1997-08-08 | 2000-11-15 | 普罗格特-甘布尔公司 | Laundry detergent compositions with amino acid based polymers to provide appearance and integrity benefits to fabrics laundered therewith |
US5897911A (en) | 1997-08-11 | 1999-04-27 | Advanced Cardiovascular Systems, Inc. | Polymer-coated stent structure |
US6121027A (en) | 1997-08-15 | 2000-09-19 | Surmodics, Inc. | Polybifunctional reagent having a polymeric backbone and photoreactive moieties and bioactive groups |
US6143370A (en) | 1997-08-27 | 2000-11-07 | Northeastern University | Process for producing polymer coatings with various porosities and surface areas |
US5972027A (en) | 1997-09-30 | 1999-10-26 | Scimed Life Systems, Inc | Porous stent drug delivery system |
US6120788A (en) | 1997-10-16 | 2000-09-19 | Bioamide, Inc. | Bioabsorbable triglycolic acid poly(ester-amide)s |
JPH11121265A (en) * | 1997-10-17 | 1999-04-30 | Toshiba Corp | Manufacture of thin-film magnetic element |
US6273908B1 (en) | 1997-10-24 | 2001-08-14 | Robert Ndondo-Lay | Stents |
US6015541A (en) | 1997-11-03 | 2000-01-18 | Micro Therapeutics, Inc. | Radioactive embolizing compositions |
EP1032328A1 (en) | 1997-11-25 | 2000-09-06 | Triad Vascular Systems Inc. | Layered endovascular graft |
US6129755A (en) | 1998-01-09 | 2000-10-10 | Nitinol Development Corporation | Intravascular stent having an improved strut configuration |
US6517534B1 (en) | 1998-02-11 | 2003-02-11 | Cosman Company, Inc. | Peri-urethral ablation |
US6140127A (en) | 1998-02-18 | 2000-10-31 | Cordis Corporation | Method of coating an intravascular stent with an endothelial cell adhesive five amino acid peptide |
WO1999042177A1 (en) | 1998-02-19 | 1999-08-26 | Radiance Medical Systems, Inc. | Radioactive stent |
US6228072B1 (en) | 1998-02-19 | 2001-05-08 | Percusurge, Inc. | Shaft for medical catheters |
US6110188A (en) | 1998-03-09 | 2000-08-29 | Corvascular, Inc. | Anastomosis method |
US6258371B1 (en) | 1998-04-03 | 2001-07-10 | Medtronic Inc | Method for making biocompatible medical article |
WO1999052574A1 (en) | 1998-04-10 | 1999-10-21 | Massachusetts Institute Of Technology | Biopolymers resistant coatings |
US20030040790A1 (en) | 1998-04-15 | 2003-02-27 | Furst Joseph G. | Stent coating |
US20010029351A1 (en) | 1998-04-16 | 2001-10-11 | Robert Falotico | Drug combinations and delivery devices for the prevention and treatment of vascular disease |
US7658727B1 (en) | 1998-04-20 | 2010-02-09 | Medtronic, Inc | Implantable medical device with enhanced biocompatibility and biostability |
US20020188037A1 (en) | 1999-04-15 | 2002-12-12 | Chudzik Stephen J. | Method and system for providing bioactive agent release coating |
ATE219693T1 (en) | 1998-04-27 | 2002-07-15 | Surmodics Inc | BIOACTIVE ACTIVE COATINGS |
US6013099A (en) | 1998-04-29 | 2000-01-11 | Medtronic, Inc. | Medical device for delivering a water-insoluble therapeutic salt or substance |
US6113629A (en) | 1998-05-01 | 2000-09-05 | Micrus Corporation | Hydrogel for the therapeutic treatment of aneurysms |
KR100314496B1 (en) | 1998-05-28 | 2001-11-22 | 윤동진 | Non-thrombogenic heparin derivatives, process for preparation and use thereof |
WO1999062572A1 (en) | 1998-06-03 | 1999-12-09 | N.V. Bekaert S.A. | Stents with a diamond like coating |
US6106889A (en) | 1998-06-11 | 2000-08-22 | Biocoat Incorporated | Method of selective coating of articles |
US6171334B1 (en) | 1998-06-17 | 2001-01-09 | Advanced Cardiovascular Systems, Inc. | Expandable stent and method of use |
US6153252A (en) | 1998-06-30 | 2000-11-28 | Ethicon, Inc. | Process for coating stents |
US6010573A (en) | 1998-07-01 | 2000-01-04 | Virginia Commonwealth University | Apparatus and method for endothelial cell seeding/transfection of intravascular stents |
DE69907686T2 (en) | 1998-07-21 | 2004-02-26 | Biocompatibles Uk Ltd., Farnham | COATING |
US6299604B1 (en) | 1998-08-20 | 2001-10-09 | Cook Incorporated | Coated implantable medical device |
US6248127B1 (en) | 1998-08-21 | 2001-06-19 | Medtronic Ave, Inc. | Thromboresistant coated medical device |
US6335029B1 (en) | 1998-08-28 | 2002-01-01 | Scimed Life Systems, Inc. | Polymeric coatings for controlled delivery of active agents |
US6068202A (en) | 1998-09-10 | 2000-05-30 | Precision Valve & Automotion, Inc. | Spraying and dispensing apparatus |
US6011125A (en) | 1998-09-25 | 2000-01-04 | General Electric Company | Amide modified polyesters |
US6206915B1 (en) | 1998-09-29 | 2001-03-27 | Medtronic Ave, Inc. | Drug storing and metering stent |
EP1726271B1 (en) | 1998-09-30 | 2012-07-25 | Bard Peripheral Vascular, Inc. | Selective adherence of stentgraft coverings, mandrel and method of making stent-graft device |
US6165267A (en) | 1998-10-07 | 2000-12-26 | Sandia Corporation | Spin coating apparatus |
US6407009B1 (en) | 1998-11-12 | 2002-06-18 | Advanced Micro Devices, Inc. | Methods of manufacture of uniform spin-on films |
US6575933B1 (en) | 1998-11-30 | 2003-06-10 | Cryocath Technologies Inc. | Mechanical support for an expandable membrane |
US6358567B2 (en) | 1998-12-23 | 2002-03-19 | The Regents Of The University Of California | Colloidal spray method for low cost thin coating deposition |
US6120847A (en) | 1999-01-08 | 2000-09-19 | Scimed Life Systems, Inc. | Surface treatment method for stent coating |
US6530950B1 (en) | 1999-01-12 | 2003-03-11 | Quanam Medical Corporation | Intraluminal stent having coaxial polymer member |
US6419692B1 (en) | 1999-02-03 | 2002-07-16 | Scimed Life Systems, Inc. | Surface protection method for stents and balloon catheters for drug delivery |
US6143354A (en) | 1999-02-08 | 2000-11-07 | Medtronic Inc. | One-step method for attachment of biomolecules to substrate surfaces |
US6273910B1 (en) | 1999-03-11 | 2001-08-14 | Advanced Cardiovascular Systems, Inc. | Stent with varying strut geometry |
US6364903B2 (en) | 1999-03-19 | 2002-04-02 | Meadox Medicals, Inc. | Polymer coated stent |
US6059714A (en) | 1999-03-26 | 2000-05-09 | Implant Sciences Corporation | Radioactive medical devices |
US6372283B1 (en) | 1999-04-02 | 2002-04-16 | Medtronic, Inc. | Plasma process for surface modification of pyrolitic carbon |
JP3398936B2 (en) | 1999-04-09 | 2003-04-21 | 日本エー・エス・エム株式会社 | Semiconductor processing equipment |
US6368658B1 (en) | 1999-04-19 | 2002-04-09 | Scimed Life Systems, Inc. | Coating medical devices using air suspension |
US6156373A (en) | 1999-05-03 | 2000-12-05 | Scimed Life Systems, Inc. | Medical device coating methods and devices |
WO2000079221A1 (en) * | 1999-06-24 | 2000-12-28 | Mitsui Mining & Smelting Co., Ltd. | Flow rate sensor unit, flowmeter and flow sensor |
US6258121B1 (en) | 1999-07-02 | 2001-07-10 | Scimed Life Systems, Inc. | Stent coating |
US6283947B1 (en) | 1999-07-13 | 2001-09-04 | Advanced Cardiovascular Systems, Inc. | Local drug delivery injection catheter |
US6494862B1 (en) | 1999-07-13 | 2002-12-17 | Advanced Cardiovascular Systems, Inc. | Substance delivery apparatus and a method of delivering a therapeutic substance to an anatomical passageway |
US6177523B1 (en) | 1999-07-14 | 2001-01-23 | Cardiotech International, Inc. | Functionalized polyurethanes |
US6790228B2 (en) | 1999-12-23 | 2004-09-14 | Advanced Cardiovascular Systems, Inc. | Coating for implantable devices and a method of forming the same |
US6713119B2 (en) | 1999-09-03 | 2004-03-30 | Advanced Cardiovascular Systems, Inc. | Biocompatible coating for a prosthesis and a method of forming the same |
US6379381B1 (en) | 1999-09-03 | 2002-04-30 | Advanced Cardiovascular Systems, Inc. | Porous prosthesis and a method of depositing substances into the pores |
US6503556B2 (en) | 2000-12-28 | 2003-01-07 | Advanced Cardiovascular Systems, Inc. | Methods of forming a coating for a prosthesis |
US6749626B1 (en) | 2000-03-31 | 2004-06-15 | Advanced Cardiovascular Systems, Inc. | Actinomycin D for the treatment of vascular disease |
US6759054B2 (en) | 1999-09-03 | 2004-07-06 | Advanced Cardiovascular Systems, Inc. | Ethylene vinyl alcohol composition and coating |
US6503954B1 (en) | 2000-03-31 | 2003-01-07 | Advanced Cardiovascular Systems, Inc. | Biocompatible carrier containing actinomycin D and a method of forming the same |
US6287628B1 (en) | 1999-09-03 | 2001-09-11 | Advanced Cardiovascular Systems, Inc. | Porous prosthesis and a method of depositing substances into the pores |
US20040029952A1 (en) | 1999-09-03 | 2004-02-12 | Yung-Ming Chen | Ethylene vinyl alcohol composition and coating |
US6183503B1 (en) * | 1999-09-17 | 2001-02-06 | Applied Medical Resources Corporation | Mesh stent with variable hoop strength |
US6203551B1 (en) | 1999-10-04 | 2001-03-20 | Advanced Cardiovascular Systems, Inc. | Chamber for applying therapeutic substances to an implant device |
US6387123B1 (en) | 1999-10-13 | 2002-05-14 | Advanced Cardiovascular Systems, Inc. | Stent with radiopaque core |
US6331313B1 (en) | 1999-10-22 | 2001-12-18 | Oculex Pharmaceticals, Inc. | Controlled-release biocompatible ocular drug delivery implant devices and methods |
US6521284B1 (en) | 1999-11-03 | 2003-02-18 | Scimed Life Systems, Inc. | Process for impregnating a porous material with a cross-linkable composition |
US6610087B1 (en) | 1999-11-16 | 2003-08-26 | Scimed Life Systems, Inc. | Endoluminal stent having a matched stiffness region and/or a stiffness gradient and methods for providing stent kink resistance |
US6251136B1 (en) | 1999-12-08 | 2001-06-26 | Advanced Cardiovascular Systems, Inc. | Method of layering a three-coated stent using pharmacological and polymeric agents |
US6613432B2 (en) | 1999-12-22 | 2003-09-02 | Biosurface Engineering Technologies, Inc. | Plasma-deposited coatings, devices and methods |
US6908624B2 (en) | 1999-12-23 | 2005-06-21 | Advanced Cardiovascular Systems, Inc. | Coating for implantable devices and a method of forming the same |
US6283949B1 (en) | 1999-12-27 | 2001-09-04 | Advanced Cardiovascular Systems, Inc. | Refillable implantable drug delivery pump |
WO2001047572A2 (en) | 1999-12-29 | 2001-07-05 | Advanced Cardiovascular Systems, Inc. | Device and active component for inhibiting formation of thrombus-inflammatory cell matrix |
US6527801B1 (en) | 2000-04-13 | 2003-03-04 | Advanced Cardiovascular Systems, Inc. | Biodegradable drug delivery material for stent |
US6387118B1 (en) | 2000-04-20 | 2002-05-14 | Scimed Life Systems, Inc. | Non-crimped stent delivery system |
US6776796B2 (en) | 2000-05-12 | 2004-08-17 | Cordis Corportation | Antiinflammatory drug and delivery device |
US20020007214A1 (en) | 2000-05-19 | 2002-01-17 | Robert Falotico | Drug/drug delivery systems for the prevention and treatment of vascular disease |
US20020007215A1 (en) | 2000-05-19 | 2002-01-17 | Robert Falotico | Drug/drug delivery systems for the prevention and treatment of vascular disease |
US20020005206A1 (en) | 2000-05-19 | 2002-01-17 | Robert Falotico | Antiproliferative drug and delivery device |
US20020007213A1 (en) | 2000-05-19 | 2002-01-17 | Robert Falotico | Drug/drug delivery systems for the prevention and treatment of vascular disease |
US6673385B1 (en) | 2000-05-31 | 2004-01-06 | Advanced Cardiovascular Systems, Inc. | Methods for polymeric coatings stents |
US6395326B1 (en) | 2000-05-31 | 2002-05-28 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for depositing a coating onto a surface of a prosthesis |
US6279368B1 (en) | 2000-06-07 | 2001-08-28 | Endovascular Technologies, Inc. | Nitinol frame heating and setting mandrel |
US6723373B1 (en) | 2000-06-16 | 2004-04-20 | Cordis Corporation | Device and process for coating stents |
US6585765B1 (en) | 2000-06-29 | 2003-07-01 | Advanced Cardiovascular Systems, Inc. | Implantable device having substances impregnated therein and a method of impregnating the same |
US20020077693A1 (en) | 2000-12-19 | 2002-06-20 | Barclay Bruce J. | Covered, coiled drug delivery stent and method |
US6555157B1 (en) | 2000-07-25 | 2003-04-29 | Advanced Cardiovascular Systems, Inc. | Method for coating an implantable device and system for performing the method |
WO2002009768A2 (en) | 2000-07-27 | 2002-02-07 | Rutgers, The State University | Therapeutic polyesters and polyamides |
US6534112B1 (en) | 2000-08-01 | 2003-03-18 | Ams Research Corporation | Semi-automatic coating system methods for coating medical devices |
US6451373B1 (en) | 2000-08-04 | 2002-09-17 | Advanced Cardiovascular Systems, Inc. | Method of forming a therapeutic coating onto a surface of an implantable prosthesis |
WO2002014078A2 (en) | 2000-08-14 | 2002-02-21 | Surface Logix, Inc. | Deformable stamp for patterning three-dimensional surfaces |
US6503538B1 (en) | 2000-08-30 | 2003-01-07 | Cornell Research Foundation, Inc. | Elastomeric functional biodegradable copolyester amides and copolyester urethanes |
US6585926B1 (en) | 2000-08-31 | 2003-07-01 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing a porous balloon |
US6562136B1 (en) | 2000-09-08 | 2003-05-13 | Surmodics, Inc. | Coating apparatus and method |
US6254632B1 (en) | 2000-09-28 | 2001-07-03 | Advanced Cardiovascular Systems, Inc. | Implantable medical device having protruding surface structures for drug delivery and cover attachment |
US6716444B1 (en) | 2000-09-28 | 2004-04-06 | Advanced Cardiovascular Systems, Inc. | Barriers for polymer-coated implantable medical devices and methods for making the same |
US6746773B2 (en) | 2000-09-29 | 2004-06-08 | Ethicon, Inc. | Coatings for medical devices |
US7261735B2 (en) | 2001-05-07 | 2007-08-28 | Cordis Corporation | Local drug delivery devices and methods for maintaining the drug coatings thereon |
US20020051730A1 (en) | 2000-09-29 | 2002-05-02 | Stanko Bodnar | Coated medical devices and sterilization thereof |
US20020111590A1 (en) | 2000-09-29 | 2002-08-15 | Davila Luis A. | Medical devices, drug coatings and methods for maintaining the drug coatings thereon |
US8153121B2 (en) * | 2000-10-06 | 2012-04-10 | Los Angeles Biomedical Research Institute at Harbor—UCLA Medical Center | Diagnosis and therapy of antibody-mediated inflammatory autoimmune disorders |
US6506437B1 (en) | 2000-10-17 | 2003-01-14 | Advanced Cardiovascular Systems, Inc. | Methods of coating an implantable device having depots formed in a surface thereof |
US6558733B1 (en) | 2000-10-26 | 2003-05-06 | Advanced Cardiovascular Systems, Inc. | Method for etching a micropatterned microdepot prosthesis |
US6758859B1 (en) | 2000-10-30 | 2004-07-06 | Kenny L. Dang | Increased drug-loading and reduced stress drug delivery device |
US6824559B2 (en) | 2000-12-22 | 2004-11-30 | Advanced Cardiovascular Systems, Inc. | Ethylene-carboxyl copolymers as drug delivery matrices |
US7077859B2 (en) | 2000-12-22 | 2006-07-18 | Avantec Vascular Corporation | Apparatus and methods for variably controlled substance delivery from implanted prostheses |
US20020082679A1 (en) | 2000-12-22 | 2002-06-27 | Avantec Vascular Corporation | Delivery or therapeutic capable agents |
US6544543B1 (en) | 2000-12-27 | 2003-04-08 | Advanced Cardiovascular Systems, Inc. | Periodic constriction of vessels to treat ischemic tissue |
US6663662B2 (en) | 2000-12-28 | 2003-12-16 | Advanced Cardiovascular Systems, Inc. | Diffusion barrier layer for implantable devices |
US6540776B2 (en) | 2000-12-28 | 2003-04-01 | Advanced Cardiovascular Systems, Inc. | Sheath for a prosthesis and methods of forming the same |
US20020087123A1 (en) | 2001-01-02 | 2002-07-04 | Hossainy Syed F.A. | Adhesion of heparin-containing coatings to blood-contacting surfaces of medical devices |
US6645195B1 (en) | 2001-01-05 | 2003-11-11 | Advanced Cardiovascular Systems, Inc. | Intraventricularly guided agent delivery system and method of use |
US6544223B1 (en) | 2001-01-05 | 2003-04-08 | Advanced Cardiovascular Systems, Inc. | Balloon catheter for delivering therapeutic agents |
US6544582B1 (en) | 2001-01-05 | 2003-04-08 | Advanced Cardiovascular Systems, Inc. | Method and apparatus for coating an implantable device |
US20030215564A1 (en) | 2001-01-18 | 2003-11-20 | Heller Phillip F. | Method and apparatus for coating an endoprosthesis |
US6740040B1 (en) | 2001-01-30 | 2004-05-25 | Advanced Cardiovascular Systems, Inc. | Ultrasound energy driven intraventricular catheter to treat ischemia |
US20030032767A1 (en) | 2001-02-05 | 2003-02-13 | Yasuhiro Tada | High-strength polyester-amide fiber and process for producing the same |
EP1463438A4 (en) | 2001-02-09 | 2008-01-23 | Endoluminal Therapeutics Inc | Endomural therapy |
DE10107795B4 (en) | 2001-02-13 | 2014-05-15 | Berlex Ag | Vascular support with a basic body, method for producing the vascular support, apparatus for coating the vascular support |
WO2002072014A2 (en) | 2001-03-08 | 2002-09-19 | Volcano Therapeutics, Inc. | Medical devices, compositions and methods for treating vulnerable plaque |
US6780424B2 (en) | 2001-03-30 | 2004-08-24 | Charles David Claude | Controlled morphologies in polymer drug for release of drugs from polymer films |
US6645135B1 (en) | 2001-03-30 | 2003-11-11 | Advanced Cardiovascular Systems, Inc. | Intravascular catheter device and method for simultaneous local delivery of radiation and a therapeutic substance |
US6623448B2 (en) | 2001-03-30 | 2003-09-23 | Advanced Cardiovascular Systems, Inc. | Steerable drug delivery device |
US6625486B2 (en) | 2001-04-11 | 2003-09-23 | Advanced Cardiovascular Systems, Inc. | Method and apparatus for intracellular delivery of an agent |
US6764505B1 (en) | 2001-04-12 | 2004-07-20 | Advanced Cardiovascular Systems, Inc. | Variable surface area stent |
US6712845B2 (en) | 2001-04-24 | 2004-03-30 | Advanced Cardiovascular Systems, Inc. | Coating for a stent and a method of forming the same |
EP2283845A1 (en) | 2001-04-26 | 2011-02-16 | pSivida Inc. | Sustained release drug delivery system containing codrugs |
US6660034B1 (en) | 2001-04-30 | 2003-12-09 | Advanced Cardiovascular Systems, Inc. | Stent for increasing blood flow to ischemic tissues and a method of using the same |
US6656506B1 (en) | 2001-05-09 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Microparticle coated medical device |
US7651695B2 (en) | 2001-05-18 | 2010-01-26 | Advanced Cardiovascular Systems, Inc. | Medicated stents for the treatment of vascular disease |
US7862495B2 (en) | 2001-05-31 | 2011-01-04 | Advanced Cardiovascular Systems, Inc. | Radiation or drug delivery source with activity gradient to minimize edge effects |
US6743462B1 (en) | 2001-05-31 | 2004-06-01 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for coating implantable devices |
US6605154B1 (en) | 2001-05-31 | 2003-08-12 | Advanced Cardiovascular Systems, Inc. | Stent mounting device |
US6666880B1 (en) | 2001-06-19 | 2003-12-23 | Advised Cardiovascular Systems, Inc. | Method and system for securing a coated stent to a balloon catheter |
US6695920B1 (en) | 2001-06-27 | 2004-02-24 | Advanced Cardiovascular Systems, Inc. | Mandrel for supporting a stent and a method of using the mandrel to coat a stent |
US6572644B1 (en) | 2001-06-27 | 2003-06-03 | Advanced Cardiovascular Systems, Inc. | Stent mounting device and a method of using the same to coat a stent |
US6565659B1 (en) | 2001-06-28 | 2003-05-20 | Advanced Cardiovascular Systems, Inc. | Stent mounting assembly and a method of using the same to coat a stent |
US6585755B2 (en) | 2001-06-29 | 2003-07-01 | Advanced Cardiovascular | Polymeric stent suitable for imaging by MRI and fluoroscopy |
US6706013B1 (en) | 2001-06-29 | 2004-03-16 | Advanced Cardiovascular Systems, Inc. | Variable length drug delivery catheter |
US6656216B1 (en) | 2001-06-29 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Composite stent with regioselective material |
US6682771B2 (en) | 2001-07-02 | 2004-01-27 | Scimed Life Systems, Inc. | Coating dispensing system and method using a solenoid head for coating medical devices |
EP1273314A1 (en) | 2001-07-06 | 2003-01-08 | Terumo Kabushiki Kaisha | Stent |
US6641611B2 (en) | 2001-11-26 | 2003-11-04 | Swaminathan Jayaraman | Therapeutic coating for an intravascular implant |
US6640738B2 (en) * | 2001-09-05 | 2003-11-04 | Robert A. Pierce | Bitt with rotatable line-handling surface |
JP2005504813A (en) | 2001-09-24 | 2005-02-17 | メドトロニック・エイヴイイー・インコーポレーテッド | Rational drug therapy device and method |
US7195640B2 (en) | 2001-09-25 | 2007-03-27 | Cordis Corporation | Coated medical devices for the treatment of vulnerable plaque |
US6753071B1 (en) | 2001-09-27 | 2004-06-22 | Advanced Cardiovascular Systems, Inc. | Rate-reducing membrane for release of an agent |
US20030059520A1 (en) | 2001-09-27 | 2003-03-27 | Yung-Ming Chen | Apparatus for regulating temperature of a composition and a method of coating implantable devices |
US20030065377A1 (en) | 2001-09-28 | 2003-04-03 | Davila Luis A. | Coated medical devices |
US20030073961A1 (en) | 2001-09-28 | 2003-04-17 | Happ Dorrie M. | Medical device containing light-protected therapeutic agent and a method for fabricating thereof |
US20030088307A1 (en) | 2001-11-05 | 2003-05-08 | Shulze John E. | Potent coatings for stents |
US7585516B2 (en) | 2001-11-12 | 2009-09-08 | Advanced Cardiovascular Systems, Inc. | Coatings for drug delivery devices |
US6517889B1 (en) | 2001-11-26 | 2003-02-11 | Swaminathan Jayaraman | Process for coating a surface of a stent |
US6663880B1 (en) | 2001-11-30 | 2003-12-16 | Advanced Cardiovascular Systems, Inc. | Permeabilizing reagents to increase drug delivery and a method of local delivery |
US6709514B1 (en) | 2001-12-28 | 2004-03-23 | Advanced Cardiovascular Systems, Inc. | Rotary coating apparatus for coating implantable medical devices |
US7789908B2 (en) * | 2002-06-25 | 2010-09-07 | Boston Scientific Scimed, Inc. | Elastomerically impregnated ePTFE to enhance stretch and recovery properties for vascular grafts and coverings |
US20040054104A1 (en) | 2002-09-05 | 2004-03-18 | Pacetti Stephen D. | Coatings for drug delivery devices comprising modified poly(ethylene-co-vinyl alcohol) |
US20040063805A1 (en) | 2002-09-19 | 2004-04-01 | Pacetti Stephen D. | Coatings for implantable medical devices and methods for fabrication thereof |
US6818063B1 (en) | 2002-09-24 | 2004-11-16 | Advanced Cardiovascular Systems, Inc. | Stent mandrel fixture and method for minimizing coating defects |
US7087263B2 (en) | 2002-10-09 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Rare limiting barriers for implantable medical devices |
US7169172B2 (en) * | 2002-11-01 | 2007-01-30 | Counter Clockwise, Inc. | Method and apparatus for caged stent delivery |
US6862794B2 (en) * | 2003-03-03 | 2005-03-08 | Medtronic Ave, Inc. | Method for manufacturing an endovascular support device |
US7077910B2 (en) * | 2003-04-07 | 2006-07-18 | Surmodics, Inc. | Linear rail coating apparatus and method |
US7482034B2 (en) | 2003-04-24 | 2009-01-27 | Boston Scientific Scimed, Inc. | Expandable mask stent coating method |
US7744645B2 (en) * | 2003-09-29 | 2010-06-29 | Medtronic Vascular, Inc. | Laminated drug-polymer coated stent with dipped and cured layers |
US7198675B2 (en) | 2003-09-30 | 2007-04-03 | Advanced Cardiovascular Systems | Stent mandrel fixture and method for selectively coating surfaces of a stent |
US7704544B2 (en) | 2003-10-07 | 2010-04-27 | Advanced Cardiovascular Systems, Inc. | System and method for coating a tubular implantable medical device |
US7823533B2 (en) * | 2005-06-30 | 2010-11-02 | Advanced Cardiovascular Systems, Inc. | Stent fixture and method for reducing coating defects |
-
2005
- 2005-06-30 US US11/174,195 patent/US7823533B2/en not_active Expired - Fee Related
-
2006
- 2006-06-16 WO PCT/US2006/023636 patent/WO2007005246A1/en active Application Filing
-
2010
- 2010-09-24 US US12/890,536 patent/US8343568B2/en not_active Expired - Fee Related
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6673154B1 (en) * | 2001-06-28 | 2004-01-06 | Advanced Cardiovascular Systems, Inc. | Stent mounting device to coat a stent |
US6527863B1 (en) * | 2001-06-29 | 2003-03-04 | Advanced Cardiovascular Systems, Inc. | Support device for a stent and a method of using the same to coat a stent |
WO2004008995A2 (en) * | 2002-07-19 | 2004-01-29 | Boston Scientific Limited | Stent coating holders |
Also Published As
Publication number | Publication date |
---|---|
US20070003688A1 (en) | 2007-01-04 |
US8343568B2 (en) | 2013-01-01 |
US20110076386A1 (en) | 2011-03-31 |
US7823533B2 (en) | 2010-11-02 |
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