CA2430126A1 - Method for manufacturing a medical device having a coated portion by laser ablation - Google Patents
Method for manufacturing a medical device having a coated portion by laser ablation Download PDFInfo
- Publication number
- CA2430126A1 CA2430126A1 CA002430126A CA2430126A CA2430126A1 CA 2430126 A1 CA2430126 A1 CA 2430126A1 CA 002430126 A CA002430126 A CA 002430126A CA 2430126 A CA2430126 A CA 2430126A CA 2430126 A1 CA2430126 A1 CA 2430126A1
- Authority
- CA
- Canada
- Prior art keywords
- coating
- coated
- medical device
- coating material
- plate
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Classifications
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K26/00—Working by laser beam, e.g. welding, cutting or boring
- B23K26/36—Removing material
- B23K26/38—Removing material by boring or cutting
- B23K26/382—Removing material by boring or cutting by boring
-
- 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
-
- 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
-
- 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
- A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K26/00—Working by laser beam, e.g. welding, cutting or boring
- B23K26/02—Positioning or observing the workpiece, e.g. with respect to the point of impact; Aligning, aiming or focusing the laser beam
- B23K26/06—Shaping the laser beam, e.g. by masks or multi-focusing
- B23K26/062—Shaping the laser beam, e.g. by masks or multi-focusing by direct control of the laser beam
- B23K26/0622—Shaping the laser beam, e.g. by masks or multi-focusing by direct control of the laser beam by shaping pulses
- B23K26/0624—Shaping the laser beam, e.g. by masks or multi-focusing by direct control of the laser beam by shaping pulses using ultrashort pulses, i.e. pulses of 1ns or less
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K26/00—Working by laser beam, e.g. welding, cutting or boring
- B23K26/36—Removing material
- B23K26/40—Removing material taking account of the properties of the material involved
-
- 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
- A61F2240/00—Manufacturing or designing of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2240/001—Designing or manufacturing processes
-
- 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
- A61L2400/00—Materials characterised by their function or physical properties
- A61L2400/18—Modification of implant surfaces in order to improve biocompatibility, cell growth, fixation of biomolecules, e.g. plasma treatment
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2101/00—Articles made by soldering, welding or cutting
- B23K2101/34—Coated articles, e.g. plated or painted; Surface treated articles
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2103/00—Materials to be soldered, welded or cut
- B23K2103/02—Iron or ferrous alloys
- B23K2103/04—Steel or steel alloys
- B23K2103/05—Stainless steel
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2103/00—Materials to be soldered, welded or cut
- B23K2103/08—Non-ferrous metals or alloys
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2103/00—Materials to be soldered, welded or cut
- B23K2103/08—Non-ferrous metals or alloys
- B23K2103/14—Titanium or alloys thereof
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2103/00—Materials to be soldered, welded or cut
- B23K2103/16—Composite materials, e.g. fibre reinforced
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2103/00—Materials to be soldered, welded or cut
- B23K2103/30—Organic material
- B23K2103/42—Plastics
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2103/00—Materials to be soldered, welded or cut
- B23K2103/50—Inorganic material, e.g. metals, not provided for in B23K2103/02 – B23K2103/26
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
- B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
- B23K2103/00—Materials to be soldered, welded or cut
- B23K2103/50—Inorganic material, e.g. metals, not provided for in B23K2103/02 – B23K2103/26
- B23K2103/52—Ceramics
Abstract
The present invention is directed to a method for manufacturing a medical device having a coated portion which comprises obtaining a structure having an inner surface and an outer surface; coating at least a portion of the inner or outer surface with a first coating material; and ablating the coated tubular structure with ultrashort laser pulses to form at least one opening therein to form the coated portion. A plate can be used instead of the structure, and the plate is folded to form the structure after the ablation. A plurality of medical devices, e.g. stents, made of any materials and having uniform coating(s), can be easily manufactured by the method of the present invention.
Description
METHOD FOR MANUFACTURING A MEDICAL DEVICE
HAVING A COATED PORTION BY LASER ABLATION
FIELD OF THE INVENTION
This invention relates generally to a method for manufacturing a medical device. More particularly, the invention is directed to a method for manufacturing a medical device having a coated portion by laser ablation.
BACKGROUND OF THE INVENTION
~pl~table medical devices, such as prosthesis or stems, are used to reduce restenosis after balloon angioplasty or other procedures involving catheters.
Usually, the suitable medical device or stmt is cylindrical in shape. The walls of the cylindrical structure can be formed of metal or polymer with openings therein, e.g., a mesh. The stent is implanted into a body lumen, such as a blood vessel, where it stays permanently, to keep the vessel open and to improve blood flow to the heart muscle and relieve symptoms. Stems can also be positioned in other parts of the body, such as the kidneys or the brain. The stmt procedure is fairly common, and various types of stems have been developed and actually used. However, since the bare metal surface of the scents may trigger restenosis, the stmt surface should be altered to make it more biocompatible. Scents coated with polymers have been offered to reduce likelihood of restenosis caused by the metal surface of stems.
Further, there are various types of polymer coats for stems which contain drugs which are delivered to an afflicted area of a body lumen. Drugs may be either bonded chemically, physically or absorbed in the polymer matrix. Also, for the purpose of obtaining drug delivery stems, the drugs may be directly coated or inunobilized onto the stents, e.g. using a binding molecule between the drug molecule and the stmt surface.
Previously, such coated stems have been manufactured by shaping the body of the stems first by photo-etching, laser ablation, electron beam ablation, or any other means, and then coating the stents with polymer compositions or drug compositions by dip-coating, spray-coating or any other means. However, due to the complex geometry of the scent, applying an even coating on a metal stmt is very difficult. Therefore, methods for easily manufacturing a stmt with uniform coatings) are necessary.
In addition, the polymer coating, when applied by methods in the art, tends to create bridges at small gaps or corners between stmt struts. Also, in the conventional methods, wherein a coating process takes place after a shaping process, it is alinost impossible to selectively coat the stent. For example, it is impossible to coat one side of a stmt without coating the other side or to apply different coatings to the outside and inside of a stmt. Therefore, there is a need for methods of making a stmt, especially coated stmt, wherein the coatings) does not form bridges at gaps or corners, and wherein selective coating of the stmt can be readily achieved.
SUMMARY OF THE INVENTION
These and other objectives are accomplished by the present invention. To achieve the aforementioned objectives, a method has been invented for manufacturing a medical device having a coated portion by laser ablation.
An embodiment of the present invention is a method for manufacturing a medical device having a coated portion which comprises obtaining a structure having an inner s~face and an outer surface. At least a portion of the inner or outer surface is coated with a first coating material. Then, the coated structure is ablated with a laser to form at least one opening therein to form the coated portion.
In another embodiment of the present invention, the method for manufacturing a medical device having a coated portion comprises obtaining a plate having a first surface and a second surface. At least a portion of the first surface or second surface is coated with a first coating material. The coated plate is then ablated with a laser to form at least one opening in the coated plate. Afterward, the coated and ablated plate is formed by folding or shaping into the medical device.
DESCRIPTION OF THE FIGURES
Fig. 1A through 1D show the steps of an embodiment of the present invention.
Fig. 1A depicts a cross-sectional view of a tubular structure.
Fig. 1B depicts a cross-sectional view of the tubular structure after a coating ~5 is applied on its inner surface.
Fig. 1C depicts a cross-sectional view ofthe tubular structure after another coating is applied on its outer surface.
Fig. 1D depicts a cross-sectional view of a coated tube-like portion of a medical device formed by ablating the tubular structure with a laser.
30 Fig. 2A through 2E show steps of another embodiment of the present invention.
Fig. 2A depicts a cross-sectional view of a plate.
Fig. 2B depicts a cross-sectional view of the plate after a coating is applied on its first surface.
35 Fig. 2C depicts a cross-sectional view of the plate after another coating is applied on its second surface.
WO 02/43619 _ _ PCT/USO1/44301 Fig. 2D depicts a cross-sectional viewYof the coated plate after laser ablation.
Fig. 2E depicts a cross-sectional view of a coated tube-like portion of a medical device made by forming the ablated plate into a desired shape.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
In a method of the present invention, a structure or a plate is coated first, and then, ablated by a laser to form openings. Such ablation may be conducted with a ultrashort-pulse laser. "Ultrashort-pulse lasers" refer to lasers (light amplification by stimulated emission of radiation) consisting of pulses with durations shorter than abut 10 pico (=10 -") second. The ultrashort-pulse laser is clearly distinguished from conventional continuous wave and long-pulse lasers (nanosecond (10 '9 sec) laser) which have significantly longer pulses.
When a material is ablated by a conventional laser, the material is removed by thermal ablation wherein the material is locally heated to near melting point or boiling point. Thus, ablation using conventional lasers has various problems. For example, the ablation is furthermore accompanied by a heat transfer and a strong thermal shock to surrounding material which might cause serious damage, such as cracking. Also, the material once removed tends to redeposit or re-solidify on the surrounding surface. Thus, a material ablated by a conventional laser must be cleaned to remove the redeposited material surrounding the cut surface. Hence, if a material having an immobilized molecule on its surface is ablated by a conventional laser, because a clearing step is required, the immobilized molecule may be washed away at the cleaning step. Also, since process parameters for a conventional laser ablation, such as boiling point and absorption of the laser light, varies according to materials to be ablated, a layered material consisting of layers made of different materials cannot be ablated by a conventional laser.
On the other hand, ablation using an ultrashort-pulse laser is free from such problems. The ultrashort-pulse deposits its energy so quickly that it does not interact at all with the plume of vaporized material, which would distort and bend the incoming beam and produce a rough-edged cut. The plasma plume leaves the surface very rapidly, ensuring that it is well beyond the cut edges before the arrival of the next laser pulse.
Since the pulse is very short, atoms in a material to be ablated are stationary in space with respect to the pulse duration. As a result, the ultrashort-pulse laser does not react differently between dielectric materials and electric materials. Thus, any material, including glasses, polymers, ceramics, silicon, and metals, can be ablated with very high precision without damage in surrounding area by ultrashort-pulse lasers due to the absence of heat shock waves. In addition, the sm'face ablated with a ultrashort-pulse laser has an excellent quality which does not need further polishing as required for a surface ablated with a conventional laser because redeposition is less or absent.
The lasers suitable for use in the method of the present invention are preferably ultrashort-pulse lasers consisting of pulses shorter than about 10 -1' second, preferably shorter than about 10 -lZ second, and most preferably shorter than about 10 -'3 second which are referred to as femtosecond lasers. The ultrashort-pulse laser used for the The intensity (fluence) of the laser radiation that is required to ablate a material is dependent on the material to be ablated. Specifically each material has its own laser-induced optical breakdown (LIOB) threshold which characterizes the fluence required to ablate the material at a particular pulse width. Also the fluence of the ultrashort-pulse Iaser suitable for the present invention can be chosen according to the thickness of the tube wall, the thickness of the coating and each material. Furthermore, the number of pulses needed to ablate completely through a material can be calculated for a given energy or fluence.
For example, a hole without any redeposition can be drilled into a 0.7 mm-tick stainless steel plate coated with a 0.3 mm-thick polyethylene terephthalate) coating on its one surface, using a laser with a pulse duration of 220 femtosecond and a fluence of 0.6 J /cmz at a wavelength of 780 nm with a repetition rate of 1 kHz commercial femtosecond Tiaapphire laser and amplifier system (SPECTRA-PHYSICS, SPITFIRE).
As another example, a hole without any redeposition can be drilled into a 0.7 mm-thick piece of tantalum with a 0.3 mm-thick polyethylene oxide)/poly(butylene terephthalate) copolymer coating using a laser with a pulse duration of 120 femtosecond and a fluence of 0.5 J /cm2 with the same system used above.
The Iaser ablation of the present invention can be conducted using any additional techniques for improved accuracy and efficiency of such ultrashort-pulse laser ablation, e.g. diffractive optical elements (DOES) and/or polarization trepanning. See C.
Momma et aL, Beam deliuery of femtosecoh.d laser radiation by diff~active optical elemefzts, Appl. Phys. A 67, 517-520 (1998); S. Nolte et al., PolaYizatioh effects in ult~ashof~t pulse lase~° d~illi~zg, Appl. Phys. A 68, 563-567 (1999), both are incorporated herein by reference.
The ultrashort-pulse lasers are known to artisans. For example, they are thoroughly disclosed by M.D. Perry et a1. in Ultrasho~t-Pulse Laser Machining, Section K-ICALEO 1998, pp. l-20, which is incorporated herein by reference.
An embodiment of the present invention is illustrated in Figures lA-1D in which a tubular structure made of a suitable medical device material is coated with a coating material or composition. Fig. 1A depicts a cross-sectional view of a tubular structure 10 made of a suitable medical device material. The inner surface of the tubular structure 10 is coated with first coating material or composition 12 (Fig. 1B). Then, the outer surface of the tubular structure 10 is also coated with second coating material or composition 14 (Fig.
1C) which can be the same as the first coating material or composition. The tubular structure 10 having an inner coating 12 and outer coating 14 is ablated by an ultrashort-pulse laser to form openings that made up a geometric pattern in the tubular structure (Fig.
1D). In this manner, a coated tube-like portion of a medical device 16 is formed.
Alternatively, only one of the surfaces, e.g. inner or outer, may be coated.
Another embodiment is illustrated in Figures 2A-2E. Fig. 2A depicts a cross-sectional view of a plate 20 made of a suitable medical device material.
A first surface of the plate 20 is coated with first coating material or composition 22 (Fig. 2B).
Then, the second surface of the plate 20 is also coated with second coating material or composition 24, which can be the same as the first coating material or composition (Fig.
2C). The plate 20 having first coating 22 and second coating 24 is ablated by an ultrashort-pulse laser to form openings that make up a geometric pattern (Fig. 2D). The plate is then folded into a desired shape to form a coated tube-like portion of a medical device 26.
The term "structure" used in relation to a medical device means any structure ~'~'~ch is at least a part of a medical device, such as a tubular structure.
Likewise, the term "coated portion" used in relation to a medical device means any portion of a medical device which has (a) coatings) on its surface(s). An example of such coated portion is a coated tube-like portion. Medical devices that can be fabricated by the method of the present invention includes those that include a tube-like or cylindrical-like portion.
The tube-like portion of the medical device need not to be completely cylindrical. For instance, the cross-section of the tube-like portion call be any shape, such as rectangle, a triangle, etc., not just a circle. Such devices include, without limitation, stems and grafts. A
bifurcated stmt is also included among the medical devices which can be fabricated by the method of the present invention.
Preferably, the medical device is a stmt. Stems suitable for the present invention include vascular stems such as self expanding stems and balloon expandable stems. Examples of self expanding stems are illustrated in U.S. Patent Nos.
4,655,771 and 4,954,126 issued to WaIIsten and 5,061,275 issued to Wallsten et al. Examples of appropriate balloon-expandable stems are shown in 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.
Appropriate materials for making the medical device are not limited for the present invention, and any material including ceramics, polymers and metals can be used for manufacturing the device by the method of the present invention. Preferably, the device is made of a biocompatible material. Examples for such polymers include polyethylene terephthalate), polyacetal, poly(lactic acid), polyethylene oxide)/poly(butylene terephthalate) copolymer, and polycarbonate. Examples for such metals include titanium, stainless steel, platinum, tantalum or goldlplatinum alloy.
In the present invention, the term "coating" encompasses all ways of coating, such as using plasma, dipping, spraying, etching, covering, plating, co-extruding and all modern chemical ways of attaching bio-molecules to surfaces as well as conventional coating. The surface is coated with a material by a method known to the artisans, such as dipping into a polymer, spraying a coating composition onto the surface, or attaching bio-molecules to surfaces. The surface of the structure or plate is optionally subjected to a pre-treatment, such as roughing, oxidizing or adding a primer, and then coated.
Adding a primer is preferable as such pre-treatment. In another embodiment, the structure or plate °~ be covered with a film. Further, in another embodiment, the structure or plate can be made by co-extrusion of the medical device material and the coating material.
More than one coating method can be used to make a medical device. Thickness of coatings can range from almost a single layer of molecules to about 0.1 mm. Suitable thickness as of the coating are known in the art and can be selected by artisans.
Medical devices coating materials suitable for the present invention include any coating material for the stmt which are known to the skilled artisan.
Suitable coating materials include, without limitation, metals, such as tantalum, stainless steel, nitinol, titanium, and alloys, polymeric materials, such as poly L-lactic acid, polycarbonate, polyethylene terephtalate, silicones, polyurethanes, thermoplastic elastomers, ethylene vinyl acetate copolymers, polyolefin elastomers, hydrogels and EPDM rubbers. Such coatings include biologically active molecules, such as heparine or insuline molecules, directly attached to oxide molecules on the surface of the structure as explained below.
Also, the coating can be a drug-releasing coating which immediately or gradually releases a biologically active material. Coating polymer useful for drug coating includes hydrogel polymers which are often used to contain the biologically active material and are disclosed in U.S. Patent No. 5,304,121, U.S. Patent No. 5,464,650, PCT
publication W095/03083 and U.S. Patent No. 5,120,322, which are incorporated by reference.
However, a non-hydrogel can be also used. Although polymeric molecules can be combined with biologically active molecules, biologically active materials can be directly Immobilized on the surface. As disclosed in U.S. Patent No. 5,356,433 to Rowland et al., polysaccharides can be immobilized to metallic surfaces by applying an organosilane coating with amine functionality and then applying a polysaccharide using carbodiimide as a coupling gent. U.S. Patent No. 5,336,518 to Narayanan et al. also discloses that a polysaccharide can be immobilized on a surface by applying a coat of heptafluorobutylmethacrylate (HFBMA) by radiofrequency (RF) plasma deposition, creating functional groups on the surface by RF plasma with water vapor, and then applying the polysaccharide using carbodiimide. Moreover, examples of medical devices, in particular, stents coated with polymer l biologically active material coatings are described in U.S. Patent No. 5,879,697 which is incorporated herein by reference.
The term "biologically active material" encompasses therapeutic agents, such as drugs, and also genetic materials and biological materials. The genetic materials mean DNA or RNA, including, without limitation, of DNA/RNA encoding a useful protein stated below, intended to be inserted into a human body including viral vectors and non-viral vectors. Viral vectors include adenoviruses, gutted adenoviruses, adeno-associated virus, retroviruses, alpha virus (Semliki Forest, Sindbis, etc.), lentiviruses, herpes simplex virus, ex vivo modified cells (e.g., stem cells, fibroblasts, myoblasts, satellite cells, pericytes, c~diomyocytes, sketetal myocytes, macrophage), replication competent viruses (e.g., ONYX-O15), and hybrid vectors. Non-viral vectors include artificial chromosomes and mini-chromosomes, plasmid DNA vectors (e.g., pCOR), cationic polymers (e.g., polyethyleneimine, polyethyleneimine (PEI)) graft copolymers (e.g., polyether-PEI and polyethylene oxide-PEI), neutral polymers PVP, SP1017 (SUPRATEK), lipids or lipoplexes, nanoparticles and microparticles with and without targeting sequences such as the protein transduction domain (PTD). The biological materials include cells, yeasts, bacteria, proteins, peptides, cytokines and hormones. Examples for peptides and proteins include growth factors (FGF, FGF-1, FGF-2, VEGF, Endotherial Mitogenic Growth Factors, and epidermal growth factors, transforming growth factor a and (3, platelet derived endothelial growth factor, platelet derived growth factor, tumor necrosis factor a, hepatocyte growth factor and insulin like growth factor ), transcription factors, proteinkinases, CD
inhibitors, thymidine kinase, and bone morphogenic proteins (BMP's), such as BMP-2, BMP-3, BMP-4, BMP-5, BMP-6 (Vgr-1), BMP-7 (OP-1), BMP-8. BMP-9, BMP-10, BMP-11, BMP-12, BMP-13, BMP-14, BMP-15, and BMP-16. Currently preferred BMP's are BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, BMP-7. These dimeric proteins can be provided as homodimers, heterodimers, or combinations thereof, alone or together with other molecules. Cells can be of human origin (autologous or allogeneic) or from an animal source (xenogeneic), genetically engineered, if desired, to deliver proteins of interest at the transplant site. The delivery media can be formulated as needed to maintain cell function and viability. Cells include whole bone marrow, bone maxrow derived mono-nuclear cells, progenitor cells (e.g., endothelial progentitor cells) stem cells (e.g., mesenchymal, hematopoietic, neuronal), pluripotent stem cells, fibroblasts, macrophage, and satellite cells.
Biologically active material also includes non-genetic therapeutic agents, such as:
_7_ ~ anti-thrombogenic agents such as heparin, heparin derivatives, urokinase, and PPack (dextrophenylalanine proline arginine chloromethylketone);
~ anti-proliferative agents such as enoxaprin, angiopeptin, or monoclonal antibodies capable of blocking smooth muscle cell proliferation, hirudin, and acetylsalicylic acid, amlodipine and doxazosin;
~ anti-inflammatory agents such as glucocorticoids, betamethasone, dexamethasone, prednisolone, corticosterone, budesonide, estrogen, sulfasalazine, and mesalamine;
~ antineoplastic/antiproliferative/anti-miotic agents such as paclitaxel, 5-fluorouracil, cisplatin, vinblastine, vincristine, epothilones, methotrexate, azathioprine, adriamycin and mutamycin; endostatin, angiostatin and thymidine kinase inhibitors, taxol and its analogs or derivatives;
~ anesthetic agents such as lidocaine, bupivacaine, and ropivacaine;
~ anti-coagulants such as D-Phe-Pro-Arg chloromethyl keton, an RGD
peptide-containing compound, heparin, antithrombin compounds, platelet receptor antagonists, anti-thrombin anticodies, anti-platelet receptor antibodies, aspirin (aspirin is also classified as an analgesic, antipyretic and anti-inflammatory drug), dipyridamole, protamine, hirudin, prostaglandin inhibitors, platelet inhibitors and tick antiplatelet peptides;
~ vascular cell growth promotors such as growth factors, Vascular Endothelial Growth Factors (FEGF, all types including VEGF-2), growth factor receptors, transcriptional activators, and translational promotors;
~ vascular cell growth inhibitors such as antiproliferative agents, growth factor inhibitors, growth factor receptor antagonists, transcriptional repressors, translational repressors, replication inhibitors, inhibitory antibodies, antibodies directed against growth factors, bifunctional molecules consisting of a growth factor ~d a cytotoxin, bifunctional molecules consisting of an antibody and a cytotoxin;
~ cholesterol-lowering agents; vasodilating agents; and agents which interfere with endogenous vasoactive mechanisms;
~ anti-oxidants, such as probucol;
~ antibiotic agents, such as penicillin, cefoxitin, oxacillin, tobranycin . ~ ~giogenic substances, such as acidic and basic fibrobrast growth factors, estrogen including estradiol (E2), estriol (E3) and 17-Beta Estradiol; and ~ drugs for heart failure, such as digoxin, beta-blockers, angiotensin-converting enzyme (ACE) inhibitors including captopril and enalopril.
In the devices made by the method of the invention, both surfaces of the tube-like portion can be coated with a same material at the same time.
_g_ Also, one surface of the structure or plate need not be coated, while the other surface has a coating. A medical device having such portion is preferable for a drug-delivery medical device for delivering a biologically active material to a blood vessel surface while minimizing the amount of biologically active material which is delivered into the blood stream. Such a medical device is also preferable when the coating is easily damaged during implantation of the medical device, e.g., because of the unfolding shear-action of the delivery balloon.
Further in another embodiment, inner and outer surfaces of the portion of the medical device can be coated with different materials. For example, a stmt can have a polymer coating having an anti-thrombogenic agent on the inner surface which directly contacts blood flow and a polymer coating having an anti-inflammatory agent on the outer surface which directly contacts blood vessel wall. The inner surface and the outer surface can be coated by the different methods. Also, there can be more than one coating on a surface. Furthermore, an entire surface of the medical device is not necessarily coated.
In the present invention, the coated structure or plate is ablated by a laser to f°~ openings. The openings along with the remaining parts of the structure or plate make up the geometric pattern structure of the medical device. The structure or plate can be moved while the laser is held stationary to ablate the structure or plate into pattern, or alternatively, the laser can be programmed to move along a predetermined pattern by a method known to artisans. A combination of both, i. e. moving both the laser and the structure or plate, is also possible. In the present invention, even a coated stmt having a complex stmt pattern can be made with high precision. A medical devices having multiple coating layers and a complicated geometry pattern can also be easily manufactured by the method of the present invention without flaws such as polymer-bridges at gaps or corners.
Also, the layer thickness can be easily controlled by the method of the present invention.
In the case where a plate is coated and ablated, the plate is formed into a portion of the medical device in the way known to artisans. In case the coated portion is a tube-like portion, it is formed by forming the flat plate into a tube-like shape and attaching the opposing edges of the plate together such as by fusing the two opposing sides. A
method of fusing appropriate to a stmt material can be chosen. Methods of fusing include using by heat or using adhesive.
After the ablation of the present invention, there is no need to polish the ablated medical device to avoid rough cut surface because of the high quality of the cut surface.
Furthermore, a plurality of medical devices can be manufactured by coating one large structure and, as ablating it as explained above, cutting the structure into individual coated portions. For example, if the coated portion is a tube-like portion, a long tubular structure is coated first, and then ablated, and then cut into individual tube-like portions of medical devices. Likewise, a large plate can be coated first, cut into a smaller plate, and then formed into an individual coated structure and ablated.
Alternatively, a large coated plate can be shaped into a large coated structure, and then it is cut into individual coated structures as ablated. In this way, a plurality of medical devices be made by using one coating step. Also, all of the medical devices will have uniform coating thicknesses.
If necessary, the thickness of the coating can be easily measured before the ablation step. For example, it is very useful to know an amount of a biologically active material contained in a medical material. This amount can be calculated in the present invention by measuring the thickness of the coating after the coating is placed on the medical device. For example, based on the concentration of biologically active material in the coating composition, the thickness of the coating, the amount of biologically active material placed on the device can be determined.
The description contained herein is for purposes of illustration and not for purposes of limitation. Changes and modifications may be made to the embodiments of the description and still be within the scope of the invention. Furthermore, obvious changes, modifications or variations will occur to those skilled in the art. Also, all references cited above are incorporated herein, in their entirety, for all purposes related to this disclosure.
HAVING A COATED PORTION BY LASER ABLATION
FIELD OF THE INVENTION
This invention relates generally to a method for manufacturing a medical device. More particularly, the invention is directed to a method for manufacturing a medical device having a coated portion by laser ablation.
BACKGROUND OF THE INVENTION
~pl~table medical devices, such as prosthesis or stems, are used to reduce restenosis after balloon angioplasty or other procedures involving catheters.
Usually, the suitable medical device or stmt is cylindrical in shape. The walls of the cylindrical structure can be formed of metal or polymer with openings therein, e.g., a mesh. The stent is implanted into a body lumen, such as a blood vessel, where it stays permanently, to keep the vessel open and to improve blood flow to the heart muscle and relieve symptoms. Stems can also be positioned in other parts of the body, such as the kidneys or the brain. The stmt procedure is fairly common, and various types of stems have been developed and actually used. However, since the bare metal surface of the scents may trigger restenosis, the stmt surface should be altered to make it more biocompatible. Scents coated with polymers have been offered to reduce likelihood of restenosis caused by the metal surface of stems.
Further, there are various types of polymer coats for stems which contain drugs which are delivered to an afflicted area of a body lumen. Drugs may be either bonded chemically, physically or absorbed in the polymer matrix. Also, for the purpose of obtaining drug delivery stems, the drugs may be directly coated or inunobilized onto the stents, e.g. using a binding molecule between the drug molecule and the stmt surface.
Previously, such coated stems have been manufactured by shaping the body of the stems first by photo-etching, laser ablation, electron beam ablation, or any other means, and then coating the stents with polymer compositions or drug compositions by dip-coating, spray-coating or any other means. However, due to the complex geometry of the scent, applying an even coating on a metal stmt is very difficult. Therefore, methods for easily manufacturing a stmt with uniform coatings) are necessary.
In addition, the polymer coating, when applied by methods in the art, tends to create bridges at small gaps or corners between stmt struts. Also, in the conventional methods, wherein a coating process takes place after a shaping process, it is alinost impossible to selectively coat the stent. For example, it is impossible to coat one side of a stmt without coating the other side or to apply different coatings to the outside and inside of a stmt. Therefore, there is a need for methods of making a stmt, especially coated stmt, wherein the coatings) does not form bridges at gaps or corners, and wherein selective coating of the stmt can be readily achieved.
SUMMARY OF THE INVENTION
These and other objectives are accomplished by the present invention. To achieve the aforementioned objectives, a method has been invented for manufacturing a medical device having a coated portion by laser ablation.
An embodiment of the present invention is a method for manufacturing a medical device having a coated portion which comprises obtaining a structure having an inner s~face and an outer surface. At least a portion of the inner or outer surface is coated with a first coating material. Then, the coated structure is ablated with a laser to form at least one opening therein to form the coated portion.
In another embodiment of the present invention, the method for manufacturing a medical device having a coated portion comprises obtaining a plate having a first surface and a second surface. At least a portion of the first surface or second surface is coated with a first coating material. The coated plate is then ablated with a laser to form at least one opening in the coated plate. Afterward, the coated and ablated plate is formed by folding or shaping into the medical device.
DESCRIPTION OF THE FIGURES
Fig. 1A through 1D show the steps of an embodiment of the present invention.
Fig. 1A depicts a cross-sectional view of a tubular structure.
Fig. 1B depicts a cross-sectional view of the tubular structure after a coating ~5 is applied on its inner surface.
Fig. 1C depicts a cross-sectional view ofthe tubular structure after another coating is applied on its outer surface.
Fig. 1D depicts a cross-sectional view of a coated tube-like portion of a medical device formed by ablating the tubular structure with a laser.
30 Fig. 2A through 2E show steps of another embodiment of the present invention.
Fig. 2A depicts a cross-sectional view of a plate.
Fig. 2B depicts a cross-sectional view of the plate after a coating is applied on its first surface.
35 Fig. 2C depicts a cross-sectional view of the plate after another coating is applied on its second surface.
WO 02/43619 _ _ PCT/USO1/44301 Fig. 2D depicts a cross-sectional viewYof the coated plate after laser ablation.
Fig. 2E depicts a cross-sectional view of a coated tube-like portion of a medical device made by forming the ablated plate into a desired shape.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
In a method of the present invention, a structure or a plate is coated first, and then, ablated by a laser to form openings. Such ablation may be conducted with a ultrashort-pulse laser. "Ultrashort-pulse lasers" refer to lasers (light amplification by stimulated emission of radiation) consisting of pulses with durations shorter than abut 10 pico (=10 -") second. The ultrashort-pulse laser is clearly distinguished from conventional continuous wave and long-pulse lasers (nanosecond (10 '9 sec) laser) which have significantly longer pulses.
When a material is ablated by a conventional laser, the material is removed by thermal ablation wherein the material is locally heated to near melting point or boiling point. Thus, ablation using conventional lasers has various problems. For example, the ablation is furthermore accompanied by a heat transfer and a strong thermal shock to surrounding material which might cause serious damage, such as cracking. Also, the material once removed tends to redeposit or re-solidify on the surrounding surface. Thus, a material ablated by a conventional laser must be cleaned to remove the redeposited material surrounding the cut surface. Hence, if a material having an immobilized molecule on its surface is ablated by a conventional laser, because a clearing step is required, the immobilized molecule may be washed away at the cleaning step. Also, since process parameters for a conventional laser ablation, such as boiling point and absorption of the laser light, varies according to materials to be ablated, a layered material consisting of layers made of different materials cannot be ablated by a conventional laser.
On the other hand, ablation using an ultrashort-pulse laser is free from such problems. The ultrashort-pulse deposits its energy so quickly that it does not interact at all with the plume of vaporized material, which would distort and bend the incoming beam and produce a rough-edged cut. The plasma plume leaves the surface very rapidly, ensuring that it is well beyond the cut edges before the arrival of the next laser pulse.
Since the pulse is very short, atoms in a material to be ablated are stationary in space with respect to the pulse duration. As a result, the ultrashort-pulse laser does not react differently between dielectric materials and electric materials. Thus, any material, including glasses, polymers, ceramics, silicon, and metals, can be ablated with very high precision without damage in surrounding area by ultrashort-pulse lasers due to the absence of heat shock waves. In addition, the sm'face ablated with a ultrashort-pulse laser has an excellent quality which does not need further polishing as required for a surface ablated with a conventional laser because redeposition is less or absent.
The lasers suitable for use in the method of the present invention are preferably ultrashort-pulse lasers consisting of pulses shorter than about 10 -1' second, preferably shorter than about 10 -lZ second, and most preferably shorter than about 10 -'3 second which are referred to as femtosecond lasers. The ultrashort-pulse laser used for the The intensity (fluence) of the laser radiation that is required to ablate a material is dependent on the material to be ablated. Specifically each material has its own laser-induced optical breakdown (LIOB) threshold which characterizes the fluence required to ablate the material at a particular pulse width. Also the fluence of the ultrashort-pulse Iaser suitable for the present invention can be chosen according to the thickness of the tube wall, the thickness of the coating and each material. Furthermore, the number of pulses needed to ablate completely through a material can be calculated for a given energy or fluence.
For example, a hole without any redeposition can be drilled into a 0.7 mm-tick stainless steel plate coated with a 0.3 mm-thick polyethylene terephthalate) coating on its one surface, using a laser with a pulse duration of 220 femtosecond and a fluence of 0.6 J /cmz at a wavelength of 780 nm with a repetition rate of 1 kHz commercial femtosecond Tiaapphire laser and amplifier system (SPECTRA-PHYSICS, SPITFIRE).
As another example, a hole without any redeposition can be drilled into a 0.7 mm-thick piece of tantalum with a 0.3 mm-thick polyethylene oxide)/poly(butylene terephthalate) copolymer coating using a laser with a pulse duration of 120 femtosecond and a fluence of 0.5 J /cm2 with the same system used above.
The Iaser ablation of the present invention can be conducted using any additional techniques for improved accuracy and efficiency of such ultrashort-pulse laser ablation, e.g. diffractive optical elements (DOES) and/or polarization trepanning. See C.
Momma et aL, Beam deliuery of femtosecoh.d laser radiation by diff~active optical elemefzts, Appl. Phys. A 67, 517-520 (1998); S. Nolte et al., PolaYizatioh effects in ult~ashof~t pulse lase~° d~illi~zg, Appl. Phys. A 68, 563-567 (1999), both are incorporated herein by reference.
The ultrashort-pulse lasers are known to artisans. For example, they are thoroughly disclosed by M.D. Perry et a1. in Ultrasho~t-Pulse Laser Machining, Section K-ICALEO 1998, pp. l-20, which is incorporated herein by reference.
An embodiment of the present invention is illustrated in Figures lA-1D in which a tubular structure made of a suitable medical device material is coated with a coating material or composition. Fig. 1A depicts a cross-sectional view of a tubular structure 10 made of a suitable medical device material. The inner surface of the tubular structure 10 is coated with first coating material or composition 12 (Fig. 1B). Then, the outer surface of the tubular structure 10 is also coated with second coating material or composition 14 (Fig.
1C) which can be the same as the first coating material or composition. The tubular structure 10 having an inner coating 12 and outer coating 14 is ablated by an ultrashort-pulse laser to form openings that made up a geometric pattern in the tubular structure (Fig.
1D). In this manner, a coated tube-like portion of a medical device 16 is formed.
Alternatively, only one of the surfaces, e.g. inner or outer, may be coated.
Another embodiment is illustrated in Figures 2A-2E. Fig. 2A depicts a cross-sectional view of a plate 20 made of a suitable medical device material.
A first surface of the plate 20 is coated with first coating material or composition 22 (Fig. 2B).
Then, the second surface of the plate 20 is also coated with second coating material or composition 24, which can be the same as the first coating material or composition (Fig.
2C). The plate 20 having first coating 22 and second coating 24 is ablated by an ultrashort-pulse laser to form openings that make up a geometric pattern (Fig. 2D). The plate is then folded into a desired shape to form a coated tube-like portion of a medical device 26.
The term "structure" used in relation to a medical device means any structure ~'~'~ch is at least a part of a medical device, such as a tubular structure.
Likewise, the term "coated portion" used in relation to a medical device means any portion of a medical device which has (a) coatings) on its surface(s). An example of such coated portion is a coated tube-like portion. Medical devices that can be fabricated by the method of the present invention includes those that include a tube-like or cylindrical-like portion.
The tube-like portion of the medical device need not to be completely cylindrical. For instance, the cross-section of the tube-like portion call be any shape, such as rectangle, a triangle, etc., not just a circle. Such devices include, without limitation, stems and grafts. A
bifurcated stmt is also included among the medical devices which can be fabricated by the method of the present invention.
Preferably, the medical device is a stmt. Stems suitable for the present invention include vascular stems such as self expanding stems and balloon expandable stems. Examples of self expanding stems are illustrated in U.S. Patent Nos.
4,655,771 and 4,954,126 issued to WaIIsten and 5,061,275 issued to Wallsten et al. Examples of appropriate balloon-expandable stems are shown in 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.
Appropriate materials for making the medical device are not limited for the present invention, and any material including ceramics, polymers and metals can be used for manufacturing the device by the method of the present invention. Preferably, the device is made of a biocompatible material. Examples for such polymers include polyethylene terephthalate), polyacetal, poly(lactic acid), polyethylene oxide)/poly(butylene terephthalate) copolymer, and polycarbonate. Examples for such metals include titanium, stainless steel, platinum, tantalum or goldlplatinum alloy.
In the present invention, the term "coating" encompasses all ways of coating, such as using plasma, dipping, spraying, etching, covering, plating, co-extruding and all modern chemical ways of attaching bio-molecules to surfaces as well as conventional coating. The surface is coated with a material by a method known to the artisans, such as dipping into a polymer, spraying a coating composition onto the surface, or attaching bio-molecules to surfaces. The surface of the structure or plate is optionally subjected to a pre-treatment, such as roughing, oxidizing or adding a primer, and then coated.
Adding a primer is preferable as such pre-treatment. In another embodiment, the structure or plate °~ be covered with a film. Further, in another embodiment, the structure or plate can be made by co-extrusion of the medical device material and the coating material.
More than one coating method can be used to make a medical device. Thickness of coatings can range from almost a single layer of molecules to about 0.1 mm. Suitable thickness as of the coating are known in the art and can be selected by artisans.
Medical devices coating materials suitable for the present invention include any coating material for the stmt which are known to the skilled artisan.
Suitable coating materials include, without limitation, metals, such as tantalum, stainless steel, nitinol, titanium, and alloys, polymeric materials, such as poly L-lactic acid, polycarbonate, polyethylene terephtalate, silicones, polyurethanes, thermoplastic elastomers, ethylene vinyl acetate copolymers, polyolefin elastomers, hydrogels and EPDM rubbers. Such coatings include biologically active molecules, such as heparine or insuline molecules, directly attached to oxide molecules on the surface of the structure as explained below.
Also, the coating can be a drug-releasing coating which immediately or gradually releases a biologically active material. Coating polymer useful for drug coating includes hydrogel polymers which are often used to contain the biologically active material and are disclosed in U.S. Patent No. 5,304,121, U.S. Patent No. 5,464,650, PCT
publication W095/03083 and U.S. Patent No. 5,120,322, which are incorporated by reference.
However, a non-hydrogel can be also used. Although polymeric molecules can be combined with biologically active molecules, biologically active materials can be directly Immobilized on the surface. As disclosed in U.S. Patent No. 5,356,433 to Rowland et al., polysaccharides can be immobilized to metallic surfaces by applying an organosilane coating with amine functionality and then applying a polysaccharide using carbodiimide as a coupling gent. U.S. Patent No. 5,336,518 to Narayanan et al. also discloses that a polysaccharide can be immobilized on a surface by applying a coat of heptafluorobutylmethacrylate (HFBMA) by radiofrequency (RF) plasma deposition, creating functional groups on the surface by RF plasma with water vapor, and then applying the polysaccharide using carbodiimide. Moreover, examples of medical devices, in particular, stents coated with polymer l biologically active material coatings are described in U.S. Patent No. 5,879,697 which is incorporated herein by reference.
The term "biologically active material" encompasses therapeutic agents, such as drugs, and also genetic materials and biological materials. The genetic materials mean DNA or RNA, including, without limitation, of DNA/RNA encoding a useful protein stated below, intended to be inserted into a human body including viral vectors and non-viral vectors. Viral vectors include adenoviruses, gutted adenoviruses, adeno-associated virus, retroviruses, alpha virus (Semliki Forest, Sindbis, etc.), lentiviruses, herpes simplex virus, ex vivo modified cells (e.g., stem cells, fibroblasts, myoblasts, satellite cells, pericytes, c~diomyocytes, sketetal myocytes, macrophage), replication competent viruses (e.g., ONYX-O15), and hybrid vectors. Non-viral vectors include artificial chromosomes and mini-chromosomes, plasmid DNA vectors (e.g., pCOR), cationic polymers (e.g., polyethyleneimine, polyethyleneimine (PEI)) graft copolymers (e.g., polyether-PEI and polyethylene oxide-PEI), neutral polymers PVP, SP1017 (SUPRATEK), lipids or lipoplexes, nanoparticles and microparticles with and without targeting sequences such as the protein transduction domain (PTD). The biological materials include cells, yeasts, bacteria, proteins, peptides, cytokines and hormones. Examples for peptides and proteins include growth factors (FGF, FGF-1, FGF-2, VEGF, Endotherial Mitogenic Growth Factors, and epidermal growth factors, transforming growth factor a and (3, platelet derived endothelial growth factor, platelet derived growth factor, tumor necrosis factor a, hepatocyte growth factor and insulin like growth factor ), transcription factors, proteinkinases, CD
inhibitors, thymidine kinase, and bone morphogenic proteins (BMP's), such as BMP-2, BMP-3, BMP-4, BMP-5, BMP-6 (Vgr-1), BMP-7 (OP-1), BMP-8. BMP-9, BMP-10, BMP-11, BMP-12, BMP-13, BMP-14, BMP-15, and BMP-16. Currently preferred BMP's are BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, BMP-7. These dimeric proteins can be provided as homodimers, heterodimers, or combinations thereof, alone or together with other molecules. Cells can be of human origin (autologous or allogeneic) or from an animal source (xenogeneic), genetically engineered, if desired, to deliver proteins of interest at the transplant site. The delivery media can be formulated as needed to maintain cell function and viability. Cells include whole bone marrow, bone maxrow derived mono-nuclear cells, progenitor cells (e.g., endothelial progentitor cells) stem cells (e.g., mesenchymal, hematopoietic, neuronal), pluripotent stem cells, fibroblasts, macrophage, and satellite cells.
Biologically active material also includes non-genetic therapeutic agents, such as:
_7_ ~ anti-thrombogenic agents such as heparin, heparin derivatives, urokinase, and PPack (dextrophenylalanine proline arginine chloromethylketone);
~ anti-proliferative agents such as enoxaprin, angiopeptin, or monoclonal antibodies capable of blocking smooth muscle cell proliferation, hirudin, and acetylsalicylic acid, amlodipine and doxazosin;
~ anti-inflammatory agents such as glucocorticoids, betamethasone, dexamethasone, prednisolone, corticosterone, budesonide, estrogen, sulfasalazine, and mesalamine;
~ antineoplastic/antiproliferative/anti-miotic agents such as paclitaxel, 5-fluorouracil, cisplatin, vinblastine, vincristine, epothilones, methotrexate, azathioprine, adriamycin and mutamycin; endostatin, angiostatin and thymidine kinase inhibitors, taxol and its analogs or derivatives;
~ anesthetic agents such as lidocaine, bupivacaine, and ropivacaine;
~ anti-coagulants such as D-Phe-Pro-Arg chloromethyl keton, an RGD
peptide-containing compound, heparin, antithrombin compounds, platelet receptor antagonists, anti-thrombin anticodies, anti-platelet receptor antibodies, aspirin (aspirin is also classified as an analgesic, antipyretic and anti-inflammatory drug), dipyridamole, protamine, hirudin, prostaglandin inhibitors, platelet inhibitors and tick antiplatelet peptides;
~ vascular cell growth promotors such as growth factors, Vascular Endothelial Growth Factors (FEGF, all types including VEGF-2), growth factor receptors, transcriptional activators, and translational promotors;
~ vascular cell growth inhibitors such as antiproliferative agents, growth factor inhibitors, growth factor receptor antagonists, transcriptional repressors, translational repressors, replication inhibitors, inhibitory antibodies, antibodies directed against growth factors, bifunctional molecules consisting of a growth factor ~d a cytotoxin, bifunctional molecules consisting of an antibody and a cytotoxin;
~ cholesterol-lowering agents; vasodilating agents; and agents which interfere with endogenous vasoactive mechanisms;
~ anti-oxidants, such as probucol;
~ antibiotic agents, such as penicillin, cefoxitin, oxacillin, tobranycin . ~ ~giogenic substances, such as acidic and basic fibrobrast growth factors, estrogen including estradiol (E2), estriol (E3) and 17-Beta Estradiol; and ~ drugs for heart failure, such as digoxin, beta-blockers, angiotensin-converting enzyme (ACE) inhibitors including captopril and enalopril.
In the devices made by the method of the invention, both surfaces of the tube-like portion can be coated with a same material at the same time.
_g_ Also, one surface of the structure or plate need not be coated, while the other surface has a coating. A medical device having such portion is preferable for a drug-delivery medical device for delivering a biologically active material to a blood vessel surface while minimizing the amount of biologically active material which is delivered into the blood stream. Such a medical device is also preferable when the coating is easily damaged during implantation of the medical device, e.g., because of the unfolding shear-action of the delivery balloon.
Further in another embodiment, inner and outer surfaces of the portion of the medical device can be coated with different materials. For example, a stmt can have a polymer coating having an anti-thrombogenic agent on the inner surface which directly contacts blood flow and a polymer coating having an anti-inflammatory agent on the outer surface which directly contacts blood vessel wall. The inner surface and the outer surface can be coated by the different methods. Also, there can be more than one coating on a surface. Furthermore, an entire surface of the medical device is not necessarily coated.
In the present invention, the coated structure or plate is ablated by a laser to f°~ openings. The openings along with the remaining parts of the structure or plate make up the geometric pattern structure of the medical device. The structure or plate can be moved while the laser is held stationary to ablate the structure or plate into pattern, or alternatively, the laser can be programmed to move along a predetermined pattern by a method known to artisans. A combination of both, i. e. moving both the laser and the structure or plate, is also possible. In the present invention, even a coated stmt having a complex stmt pattern can be made with high precision. A medical devices having multiple coating layers and a complicated geometry pattern can also be easily manufactured by the method of the present invention without flaws such as polymer-bridges at gaps or corners.
Also, the layer thickness can be easily controlled by the method of the present invention.
In the case where a plate is coated and ablated, the plate is formed into a portion of the medical device in the way known to artisans. In case the coated portion is a tube-like portion, it is formed by forming the flat plate into a tube-like shape and attaching the opposing edges of the plate together such as by fusing the two opposing sides. A
method of fusing appropriate to a stmt material can be chosen. Methods of fusing include using by heat or using adhesive.
After the ablation of the present invention, there is no need to polish the ablated medical device to avoid rough cut surface because of the high quality of the cut surface.
Furthermore, a plurality of medical devices can be manufactured by coating one large structure and, as ablating it as explained above, cutting the structure into individual coated portions. For example, if the coated portion is a tube-like portion, a long tubular structure is coated first, and then ablated, and then cut into individual tube-like portions of medical devices. Likewise, a large plate can be coated first, cut into a smaller plate, and then formed into an individual coated structure and ablated.
Alternatively, a large coated plate can be shaped into a large coated structure, and then it is cut into individual coated structures as ablated. In this way, a plurality of medical devices be made by using one coating step. Also, all of the medical devices will have uniform coating thicknesses.
If necessary, the thickness of the coating can be easily measured before the ablation step. For example, it is very useful to know an amount of a biologically active material contained in a medical material. This amount can be calculated in the present invention by measuring the thickness of the coating after the coating is placed on the medical device. For example, based on the concentration of biologically active material in the coating composition, the thickness of the coating, the amount of biologically active material placed on the device can be determined.
The description contained herein is for purposes of illustration and not for purposes of limitation. Changes and modifications may be made to the embodiments of the description and still be within the scope of the invention. Furthermore, obvious changes, modifications or variations will occur to those skilled in the art. Also, all references cited above are incorporated herein, in their entirety, for all purposes related to this disclosure.
Claims (42)
We claim:
1. A method for manufacturing a medical device having a coated portion having at least one opening therein, wherein the method comprises a process for manufacturing the coated portion, and the process comprises the steps of:
(a) obtaining a structure having an inner surface and an outer surface;
(b) coating at least a portion of the inner or outer surface with a first coating material to form a coated structure; and (c) ablating through the coated structure with an ultrashort-pulse laser to form at least one opening therein.
(a) obtaining a structure having an inner surface and an outer surface;
(b) coating at least a portion of the inner or outer surface with a first coating material to form a coated structure; and (c) ablating through the coated structure with an ultrashort-pulse laser to form at least one opening therein.
2. The method of claim 1, wherein the structure is a tube-like structure.
3. The method of claim 1, wherein the medical device is a stent.
4. The method of claim 1, wherein step (b) comprises only coating the inner surface of the structure with the first coating material.
5. The method of claim 1, wherein step (b) comprises only coating the outer surface of the structure with the first coating material.
6. The method of claim 1, wherein step (b) comprises:
(i) coating the inner surface of the structure with the first coating material and (ii) coating the outer surface of the structure with a second coating material.
(i) coating the inner surface of the structure with the first coating material and (ii) coating the outer surface of the structure with a second coating material.
7. The method of claim 6, wherein the first coating material and the second coating material are the same.
8. The method of claim 1, wherein the first coating material is a coating composition and the surface is coated by dipping the surface into the coating composition.
9. The method of claim 1, wherein the first coating material is a coating composition and the surface is coated by spray-coating the coating composition onto the surface.
10. The method of claim 1, wherein the first coating material comprises a polymer and a biologically active material.
11. The method of claim 1, wherein the first coating material comprises a biologically active material, and the coating step (b) is conducted by immobilizing the first coating material onto at least of a portion of the surface.
12. The method of claim 1, wherein the coated structure is ablated to form a plurality of openings therein that define a plurality of struts.
13. The method of claim 1, which further comprises cutting the coated structure into sections to form more than one coated portion.
14. The method of claim 13, wherein the cutting step is conducted between the coating step and the ablating step.
15. A method for manufacturing a medical device having a coated portion having at least one opening therein, wherein the method comprises a process for manufacturing the coated portion, and the process comprises the steps of:
(a) obtaining a plate having a first surface and a second surface;
(b) coating at least a portion of the first surface or second surface which a first coating material;
(c) ablating through the coated plate with an ultrashort-pulse laser to form at least one opening therein; and (d) forming the coated portion with the ablated plate.
(a) obtaining a plate having a first surface and a second surface;
(b) coating at least a portion of the first surface or second surface which a first coating material;
(c) ablating through the coated plate with an ultrashort-pulse laser to form at least one opening therein; and (d) forming the coated portion with the ablated plate.
16. The method of claim 15, wherein the coated portion is a tube-like portion.
17. The method of claim 15, wherein the medical device is a stent.
18. The method of claim 15, wherein step (b) comprises only coating the first surface of the plate with the first coating material.
19. The method of claim I5, wherein step (b) comprises only coating the second surface of the plate with the first coating material.
20. The method of claim 15, wherein step (b) comprises:
(i) coating the first surface of the plate with the first coating material and (ii) coating the second surface of the plate with a second coating material.
(i) coating the first surface of the plate with the first coating material and (ii) coating the second surface of the plate with a second coating material.
21. The method of claim 15, wherein the first coating material and the second coating material are the same.
22. The method of claim 15, wherein the first coating material is a coating composition and the surface is coated by dipping the surface into the coating composition.
23. The method of claim 15, wherein the first coating material is a coating composition and the surface is coated by spray-coating the coating composition onto the surface.
24. The method of claim 15, wherein the first coating material comprises a biologically active material, and coating is conducted by immobilizing the first coating material onto at least of a portion of the surface.
25. The method of claim 15, wherein the first coating material comprises a polymer and a biologically active material.
26. The method of claim 15, wherein the coated plate is ablated to form a plurality of openings therein that define a plurality of struts.
27. The method of claim 15, which further comprises cutting the coated plate into sections to form more than one coated tube-like portion.
28. The method of claim 27, wherein the cutting step is conducted between the coating step and the ablating step.
29. The method of claim 27, wherein the coated plate is cut as it is ablated.
30. A medical device having at least a tube-like portion which is insertable or implantable into the body of a patient, wherein the portion has a first surface and a second surface which are adapted for exposure to body tissue of the patient, wherein at least a part of the first surface is covered with a coating for release of a first biologically active material, wherein the second surface is substantially free of the first biologically active material, and wherein the medical device is manufactured by the method of claim 1.
31. The device of claim 30, wherein the first surface is the outer surface of the tube-like portion and the second surface is the inner surface of the tube-like portion.
32. The device of claim 30, wherein the medical device is a stent.
33. The device of claim 30, wherein at least a part of the second surface is covered with a second coating.
34. The device of claim 33, wherein the second coating comprises a second biologically active material.
35. The medical device of claim 30, wherein the second surface is substantially free of a coating.
36. A method for manufacturing a medical device having a coated portion having at least one opening therein, wherein the method comprises a process for manufacturing the coated portion, and the process comprises the steps of:
(a) obtaining a structure having an inner surface and an outer surface;
(b) coating at least a portion of the inner or outer surface with a first coating material;
and (c) ablating through the coated structure with a laser to form at least one opening therein.
(a) obtaining a structure having an inner surface and an outer surface;
(b) coating at least a portion of the inner or outer surface with a first coating material;
and (c) ablating through the coated structure with a laser to form at least one opening therein.
37. A method for manufacturing a medical device having a coated portion having at least one opening therein, wherein the method comprises a process for manufacturing the coated portion, and the process comprises the steps of:
(a) obtaining a plate having a first surface and a second surface;
(b) coating at least a portion of the first surface or second surface which a first coating material;
(c) ablating through the coated plate with a laser to form at least one opening therein;
and (d) forming the coated portion with the ablated plate.
(a) obtaining a plate having a first surface and a second surface;
(b) coating at least a portion of the first surface or second surface which a first coating material;
(c) ablating through the coated plate with a laser to form at least one opening therein;
and (d) forming the coated portion with the ablated plate.
38. A medical device made by the method of claim 1.
39. The medical device of claim 38 which is a stent.
40. A medical device made by the method of claim 15.
41. The medical device of claim 40, wherein the structure is a tube-like structure.
42. The medical device of claim 40 which is a stent.
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/724,503 US6517888B1 (en) | 2000-11-28 | 2000-11-28 | Method for manufacturing a medical device having a coated portion by laser ablation |
US09/724,503 | 2000-11-28 | ||
PCT/US2001/044301 WO2002043619A2 (en) | 2000-11-28 | 2001-11-27 | Method for manufacturing a medical device having a coated portion by laser ablation |
Publications (1)
Publication Number | Publication Date |
---|---|
CA2430126A1 true CA2430126A1 (en) | 2002-06-06 |
Family
ID=24910671
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002430126A Abandoned CA2430126A1 (en) | 2000-11-28 | 2001-11-27 | Method for manufacturing a medical device having a coated portion by laser ablation |
Country Status (7)
Country | Link |
---|---|
US (2) | US6517888B1 (en) |
EP (2) | EP1616535A1 (en) |
JP (1) | JP2004520872A (en) |
AU (2) | AU2002236491B2 (en) |
CA (1) | CA2430126A1 (en) |
DE (1) | DE60114044T2 (en) |
WO (1) | WO2002043619A2 (en) |
Families Citing this family (248)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6240616B1 (en) * | 1997-04-15 | 2001-06-05 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing a medicated porous metal prosthesis |
US8172897B2 (en) * | 1997-04-15 | 2012-05-08 | Advanced Cardiovascular Systems, Inc. | Polymer and metal composite implantable medical devices |
US10028851B2 (en) * | 1997-04-15 | 2018-07-24 | Advanced Cardiovascular Systems, Inc. | Coatings for controlling erosion of a substrate of an implantable medical device |
US6433154B1 (en) * | 1997-06-12 | 2002-08-13 | Bristol-Myers Squibb Company | Functional receptor/kinase chimera in yeast cells |
US20030129215A1 (en) * | 1998-09-24 | 2003-07-10 | T-Ram, Inc. | Medical devices containing rapamycin analogs |
US6890546B2 (en) | 1998-09-24 | 2005-05-10 | Abbott Laboratories | Medical devices containing rapamycin analogs |
US7713297B2 (en) | 1998-04-11 | 2010-05-11 | Boston Scientific Scimed, Inc. | Drug-releasing stent with ceramic-containing layer |
US7662409B2 (en) * | 1998-09-25 | 2010-02-16 | Gel-Del Technologies, Inc. | Protein matrix materials, devices and methods of making and using thereof |
US7278195B2 (en) * | 1999-12-16 | 2007-10-09 | Israel Aircraft Industries Ltd. | Method for producing a coated medical support device |
JP2004500975A (en) * | 2000-05-16 | 2004-01-15 | リージェンツ オブ ザ ユニバーシティ オブ ミネソタ | High throughput particle generator and particle generation method using multiple nozzle spray operations |
US20040073294A1 (en) | 2002-09-20 | 2004-04-15 | Conor Medsystems, Inc. | Method and apparatus for loading a beneficial agent into an expandable medical device |
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 |
US7247338B2 (en) * | 2001-05-16 | 2007-07-24 | Regents Of The University Of Minnesota | Coating medical devices |
WO2003002243A2 (en) | 2001-06-27 | 2003-01-09 | Remon Medical Technologies Ltd. | Method and device for electrochemical formation of therapeutic species in vivo |
SE519566C2 (en) * | 2001-07-04 | 2003-03-11 | Nobel Biocare Ab | Method of Treating Implants by Coating with Calcium Phosphate and Bone Growth Stimulants |
WO2003008006A1 (en) * | 2001-07-19 | 2003-01-30 | Dempsey, Donald, J. | Bioactive surface for titanium implants |
US7285304B1 (en) * | 2003-06-25 | 2007-10-23 | Advanced Cardiovascular Systems, Inc. | Fluid treatment of a polymeric coating on an implantable medical device |
US7989018B2 (en) * | 2001-09-17 | 2011-08-02 | Advanced Cardiovascular Systems, Inc. | Fluid treatment of a polymeric coating on an implantable medical device |
US6863683B2 (en) | 2001-09-19 | 2005-03-08 | Abbott Laboratoris Vascular Entities Limited | Cold-molding process for loading a stent onto a stent delivery system |
US6764709B2 (en) * | 2001-11-08 | 2004-07-20 | Scimed Life Systems, Inc. | Method for making and measuring a coating on the surface of a medical device using an ultraviolet laser |
US7691461B1 (en) | 2002-04-01 | 2010-04-06 | Advanced Cardiovascular Systems, Inc. | Hybrid stent and method of making |
WO2003092468A2 (en) * | 2002-04-29 | 2003-11-13 | Gel-Del Technologies, Inc. | Biomatrix structural containment and fixation systems and methods of use thereof |
US6865810B2 (en) * | 2002-06-27 | 2005-03-15 | Scimed Life Systems, Inc. | Methods of making medical devices |
US7758636B2 (en) | 2002-09-20 | 2010-07-20 | Innovational Holdings Llc | Expandable medical device with openings for delivery of multiple beneficial agents |
EP1569762B1 (en) | 2002-10-22 | 2007-10-03 | Medtronic Vascular, Inc. | Stent with intermittent coating |
US20060271168A1 (en) * | 2002-10-30 | 2006-11-30 | Klaus Kleine | Degradable medical device |
US7758881B2 (en) * | 2004-06-30 | 2010-07-20 | Advanced Cardiovascular Systems, Inc. | Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device |
US8435550B2 (en) * | 2002-12-16 | 2013-05-07 | Abbot Cardiovascular Systems Inc. | Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device |
EP1610823B1 (en) | 2003-03-28 | 2011-09-28 | Innovational Holdings, LLC | Implantable medical device with continuous agent concentration gradient |
US20050070996A1 (en) * | 2003-04-08 | 2005-03-31 | Dinh Thomas Q. | Drug-eluting stent for controlled drug delivery |
US7163555B2 (en) | 2003-04-08 | 2007-01-16 | Medtronic Vascular, Inc. | Drug-eluting stent for controlled drug delivery |
US7086931B2 (en) * | 2003-04-18 | 2006-08-08 | Tdk Corporation | Magnetic head bar holding unit, lapping device, and method of lapping medium-opposing surface of thin-film magnetic head |
US6923996B2 (en) * | 2003-05-06 | 2005-08-02 | Scimed Life Systems, Inc. | Processes for producing polymer coatings for release of therapeutic agent |
DE10320262A1 (en) * | 2003-05-07 | 2004-12-02 | Meko Laserstrahl-Materialbearbeitungen E.K. | Process for producing a medical implant and an implant produced in this way |
US20040230290A1 (en) * | 2003-05-15 | 2004-11-18 | Jan Weber | Medical devices and methods of making the same |
US8465537B2 (en) * | 2003-06-17 | 2013-06-18 | Gel-Del Technologies, Inc. | Encapsulated or coated stent systems |
US7582082B2 (en) * | 2003-08-04 | 2009-09-01 | Koninklijke Philips Electronics N.V. | Device for shortening hairs by means of laser induced optical breakdown effects |
US8153591B2 (en) | 2003-08-26 | 2012-04-10 | Gel-Del Technologies, Inc. | Protein biomaterials and biocoacervates and methods of making and using thereof |
US7785653B2 (en) | 2003-09-22 | 2010-08-31 | Innovational Holdings Llc | Method and apparatus for loading a beneficial agent into an expandable medical device |
US7198675B2 (en) | 2003-09-30 | 2007-04-03 | Advanced Cardiovascular Systems | Stent mandrel fixture and method for selectively coating surfaces of a stent |
US7056337B2 (en) * | 2003-10-21 | 2006-06-06 | Cook Incorporated | Natural tissue stent |
AU2004296851A1 (en) * | 2003-12-08 | 2005-06-23 | Gel-Del Technologies, Inc. | Mucoadhesive drug delivery devices and methods of making and using thereof |
JP4811022B2 (en) * | 2004-01-23 | 2011-11-09 | 住友電気工業株式会社 | Expanded polytetrafluoroethylene porous body having fine pores and method for producing the same |
US7407684B2 (en) * | 2004-01-28 | 2008-08-05 | Boston Scientific Scimed, Inc. | Multi-step method of manufacturing a medical device |
US8685431B2 (en) * | 2004-03-16 | 2014-04-01 | Advanced Cardiovascular Systems, Inc. | Biologically absorbable coatings for implantable devices based on copolymers having ester bonds and methods for fabricating the same |
US8816244B2 (en) * | 2004-04-13 | 2014-08-26 | Boston Scientific Scimed, Inc. | Inverted stent cutting process |
GB0410749D0 (en) * | 2004-05-14 | 2004-06-16 | Dow Corning Ireland Ltd | Coating apparatus |
US20050260355A1 (en) * | 2004-05-20 | 2005-11-24 | Jan Weber | Medical devices and methods of making the same |
US20050266039A1 (en) * | 2004-05-27 | 2005-12-01 | Jan Weber | Coated medical device and method for making the same |
US8568469B1 (en) | 2004-06-28 | 2013-10-29 | Advanced Cardiovascular Systems, Inc. | Stent locking element and a method of securing a stent on a delivery system |
US8241554B1 (en) | 2004-06-29 | 2012-08-14 | Advanced Cardiovascular Systems, Inc. | Method of forming a stent pattern on a tube |
US20060020330A1 (en) * | 2004-07-26 | 2006-01-26 | Bin Huang | Method of fabricating an implantable medical device with biaxially oriented polymers |
US8778256B1 (en) | 2004-09-30 | 2014-07-15 | Advanced Cardiovascular Systems, Inc. | Deformation of a polymer tube in the fabrication of a medical article |
US8747878B2 (en) | 2006-04-28 | 2014-06-10 | Advanced Cardiovascular Systems, Inc. | Method of fabricating an implantable medical device by controlling crystalline structure |
US7731890B2 (en) * | 2006-06-15 | 2010-06-08 | Advanced Cardiovascular Systems, Inc. | Methods of fabricating stents with enhanced fracture toughness |
US8747879B2 (en) * | 2006-04-28 | 2014-06-10 | Advanced Cardiovascular Systems, Inc. | Method of fabricating an implantable medical device to reduce chance of late inflammatory response |
US7971333B2 (en) * | 2006-05-30 | 2011-07-05 | Advanced Cardiovascular Systems, Inc. | Manufacturing process for polymetric stents |
US20060041102A1 (en) * | 2004-08-23 | 2006-02-23 | Advanced Cardiovascular Systems, Inc. | Implantable devices comprising biologically absorbable polymers having constant rate of degradation and methods for fabricating the same |
US9283099B2 (en) * | 2004-08-25 | 2016-03-15 | Advanced Cardiovascular Systems, Inc. | Stent-catheter assembly with a releasable connection for stent retention |
US7229471B2 (en) * | 2004-09-10 | 2007-06-12 | Advanced Cardiovascular Systems, Inc. | Compositions containing fast-leaching plasticizers for improved performance of medical devices |
US8043553B1 (en) | 2004-09-30 | 2011-10-25 | Advanced Cardiovascular Systems, Inc. | Controlled deformation of a polymer tube with a restraining surface in fabricating a medical article |
US7875233B2 (en) | 2004-09-30 | 2011-01-25 | Advanced Cardiovascular Systems, Inc. | Method of fabricating a biaxially oriented implantable medical device |
US8173062B1 (en) | 2004-09-30 | 2012-05-08 | Advanced Cardiovascular Systems, Inc. | Controlled deformation of a polymer tube in fabricating a medical article |
FI20041515A (en) * | 2004-11-25 | 2006-05-26 | Lasermark Ab Oy | Procedure for the preparation of medical stents |
US20060122694A1 (en) * | 2004-12-03 | 2006-06-08 | Stinson Jonathan S | Medical devices and methods of making the same |
US20060125144A1 (en) * | 2004-12-14 | 2006-06-15 | Jan Weber | Stent and stent manufacturing methods |
US7632307B2 (en) * | 2004-12-16 | 2009-12-15 | Advanced Cardiovascular Systems, Inc. | Abluminal, multilayer coating constructs for drug-delivery stents |
US20060224226A1 (en) * | 2005-03-31 | 2006-10-05 | Bin Huang | In-vivo radial orientation of a polymeric implantable medical device |
US7381048B2 (en) * | 2005-04-12 | 2008-06-03 | Advanced Cardiovascular Systems, Inc. | Stents with profiles for gripping a balloon catheter and molds for fabricating stents |
US9119901B2 (en) * | 2005-04-28 | 2015-09-01 | Warsaw Orthopedic, Inc. | Surface treatments for promoting selective tissue attachment to medical impants |
US8414907B2 (en) * | 2005-04-28 | 2013-04-09 | Warsaw Orthopedic, Inc. | Coatings on medical implants to guide soft tissue healing |
US8071155B2 (en) * | 2005-05-05 | 2011-12-06 | Boston Scientific Scimed, Inc. | Medical devices and methods of making the same |
US7291166B2 (en) * | 2005-05-18 | 2007-11-06 | Advanced Cardiovascular Systems, Inc. | Polymeric stent patterns |
US7622070B2 (en) * | 2005-06-20 | 2009-11-24 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing an implantable polymeric medical device |
US7691082B2 (en) * | 2005-07-01 | 2010-04-06 | Boston Scientific Scimed, Inc. | Medical devices |
US20070038176A1 (en) * | 2005-07-05 | 2007-02-15 | Jan Weber | Medical devices with machined layers for controlled communications with underlying regions |
US7658880B2 (en) * | 2005-07-29 | 2010-02-09 | Advanced Cardiovascular Systems, Inc. | Polymeric stent polishing method and apparatus |
US7297758B2 (en) * | 2005-08-02 | 2007-11-20 | Advanced Cardiovascular Systems, Inc. | Method for extending shelf-life of constructs of semi-crystallizable polymers |
US7778684B2 (en) * | 2005-08-08 | 2010-08-17 | Boston Scientific Scimed, Inc. | MRI resonator system with stent implant |
US20070038290A1 (en) * | 2005-08-15 | 2007-02-15 | Bin Huang | Fiber reinforced composite stents |
US7476245B2 (en) * | 2005-08-16 | 2009-01-13 | Advanced Cardiovascular Systems, Inc. | Polymeric stent patterns |
US20070045252A1 (en) * | 2005-08-23 | 2007-03-01 | Klaus Kleine | Laser induced plasma machining with a process gas |
US9248034B2 (en) * | 2005-08-23 | 2016-02-02 | Advanced Cardiovascular Systems, Inc. | Controlled disintegrating implantable medical devices |
US20070045255A1 (en) * | 2005-08-23 | 2007-03-01 | Klaus Kleine | Laser induced plasma machining with an optimized process gas |
US20070112421A1 (en) * | 2005-11-14 | 2007-05-17 | O'brien Barry | Medical device with a grooved surface |
US7867547B2 (en) | 2005-12-19 | 2011-01-11 | Advanced Cardiovascular Systems, Inc. | Selectively coating luminal surfaces of stents |
US20070151961A1 (en) * | 2006-01-03 | 2007-07-05 | Klaus Kleine | Fabrication of an implantable medical device with a modified laser beam |
US20070156230A1 (en) | 2006-01-04 | 2007-07-05 | Dugan Stephen R | Stents with radiopaque markers |
US8840660B2 (en) | 2006-01-05 | 2014-09-23 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
US7951185B1 (en) | 2006-01-06 | 2011-05-31 | Advanced Cardiovascular Systems, Inc. | Delivery of a stent at an elevated temperature |
CA2641117C (en) * | 2006-01-31 | 2018-01-02 | Nanocopoeia, Inc. | Nanoparticle coating of surfaces |
US9108217B2 (en) | 2006-01-31 | 2015-08-18 | Nanocopoeia, Inc. | Nanoparticle coating of surfaces |
WO2007089881A2 (en) * | 2006-01-31 | 2007-08-09 | Regents Of The University Of Minnesota | Electrospray coating of objects |
US20070179219A1 (en) * | 2006-01-31 | 2007-08-02 | Bin Huang | Method of fabricating an implantable medical device using gel extrusion and charge induced orientation |
US8089029B2 (en) | 2006-02-01 | 2012-01-03 | Boston Scientific Scimed, Inc. | Bioabsorbable metal medical device and method of manufacture |
DE102006007231B4 (en) * | 2006-02-15 | 2009-04-09 | Acandis Gmbh & Co. Kg | Method of wrapping a stent |
US9526814B2 (en) * | 2006-02-16 | 2016-12-27 | Boston Scientific Scimed, Inc. | Medical balloons and methods of making the same |
US20070191931A1 (en) * | 2006-02-16 | 2007-08-16 | Jan Weber | Bioerodible endoprostheses and methods of making the same |
US20070239256A1 (en) * | 2006-03-22 | 2007-10-11 | Jan Weber | Medical devices having electrical circuits with multilayer regions |
US20070224235A1 (en) * | 2006-03-24 | 2007-09-27 | Barron Tenney | Medical devices having nanoporous coatings for controlled therapeutic agent delivery |
US8187620B2 (en) * | 2006-03-27 | 2012-05-29 | Boston Scientific Scimed, Inc. | Medical devices comprising a porous metal oxide or metal material and a polymer coating for delivering therapeutic agents |
US7964210B2 (en) * | 2006-03-31 | 2011-06-21 | Abbott Cardiovascular Systems Inc. | Degradable polymeric implantable medical devices with a continuous phase and discrete phase |
US8048150B2 (en) | 2006-04-12 | 2011-11-01 | Boston Scientific Scimed, Inc. | Endoprosthesis having a fiber meshwork disposed thereon |
US20070254012A1 (en) * | 2006-04-28 | 2007-11-01 | Ludwig Florian N | Controlled degradation and drug release in stents |
US8069814B2 (en) | 2006-05-04 | 2011-12-06 | Advanced Cardiovascular Systems, Inc. | Stent support devices |
US7761968B2 (en) * | 2006-05-25 | 2010-07-27 | Advanced Cardiovascular Systems, Inc. | Method of crimping a polymeric stent |
US7951194B2 (en) | 2006-05-26 | 2011-05-31 | Abbott Cardiovascular Sysetms Inc. | Bioabsorbable stent with radiopaque coating |
US8752268B2 (en) | 2006-05-26 | 2014-06-17 | Abbott Cardiovascular Systems Inc. | Method of making stents with radiopaque markers |
US7842737B2 (en) | 2006-09-29 | 2010-11-30 | Abbott Cardiovascular Systems Inc. | Polymer blend-bioceramic composite implantable medical devices |
US8343530B2 (en) * | 2006-05-30 | 2013-01-01 | Abbott Cardiovascular Systems Inc. | Polymer-and polymer blend-bioceramic composite implantable medical devices |
US20070282434A1 (en) * | 2006-05-30 | 2007-12-06 | Yunbing Wang | Copolymer-bioceramic composite implantable medical devices |
US7959940B2 (en) * | 2006-05-30 | 2011-06-14 | Advanced Cardiovascular Systems, Inc. | Polymer-bioceramic composite implantable medical devices |
US20080058916A1 (en) * | 2006-05-31 | 2008-03-06 | Bin Huang | Method of fabricating polymeric self-expandable stent |
US8034287B2 (en) | 2006-06-01 | 2011-10-11 | Abbott Cardiovascular Systems Inc. | Radiation sterilization of medical devices |
US8486135B2 (en) | 2006-06-01 | 2013-07-16 | Abbott Cardiovascular Systems Inc. | Implantable medical devices fabricated from branched polymers |
US20070282433A1 (en) * | 2006-06-01 | 2007-12-06 | Limon Timothy A | Stent with retention protrusions formed during crimping |
US20070281073A1 (en) * | 2006-06-01 | 2007-12-06 | Gale David C | Enhanced adhesion of drug delivery coatings on stents |
US20080124372A1 (en) * | 2006-06-06 | 2008-05-29 | Hossainy Syed F A | Morphology profiles for control of agent release rates from polymer matrices |
US20070286941A1 (en) * | 2006-06-13 | 2007-12-13 | Bin Huang | Surface treatment of a polymeric stent |
US8603530B2 (en) | 2006-06-14 | 2013-12-10 | Abbott Cardiovascular Systems Inc. | Nanoshell therapy |
US8048448B2 (en) | 2006-06-15 | 2011-11-01 | Abbott Cardiovascular Systems Inc. | Nanoshells for drug delivery |
US8535372B1 (en) | 2006-06-16 | 2013-09-17 | Abbott Cardiovascular Systems Inc. | Bioabsorbable stent with prohealing layer |
US20070290412A1 (en) * | 2006-06-19 | 2007-12-20 | John Capek | Fabricating a stent with selected properties in the radial and axial directions |
US8333000B2 (en) | 2006-06-19 | 2012-12-18 | Advanced Cardiovascular Systems, Inc. | Methods for improving stent retention on a balloon catheter |
US8017237B2 (en) | 2006-06-23 | 2011-09-13 | Abbott Cardiovascular Systems, Inc. | Nanoshells on polymers |
US9072820B2 (en) * | 2006-06-26 | 2015-07-07 | Advanced Cardiovascular Systems, Inc. | Polymer composite stent with polymer particles |
US20070299511A1 (en) * | 2006-06-27 | 2007-12-27 | Gale David C | Thin stent coating |
US8128688B2 (en) * | 2006-06-27 | 2012-03-06 | Abbott Cardiovascular Systems Inc. | Carbon coating on an implantable device |
US8815275B2 (en) | 2006-06-28 | 2014-08-26 | Boston Scientific Scimed, Inc. | Coatings for medical devices comprising a therapeutic agent and a metallic material |
US7794776B1 (en) | 2006-06-29 | 2010-09-14 | Abbott Cardiovascular Systems Inc. | Modification of polymer stents with radiation |
WO2008002778A2 (en) | 2006-06-29 | 2008-01-03 | Boston Scientific Limited | Medical devices with selective coating |
US7740791B2 (en) * | 2006-06-30 | 2010-06-22 | Advanced Cardiovascular Systems, Inc. | Method of fabricating a stent with features by blow molding |
US20080009938A1 (en) * | 2006-07-07 | 2008-01-10 | Bin Huang | Stent with a radiopaque marker and method for making the same |
US7823263B2 (en) | 2006-07-11 | 2010-11-02 | Abbott Cardiovascular Systems Inc. | Method of removing stent islands from a stent |
US20080014244A1 (en) * | 2006-07-13 | 2008-01-17 | Gale David C | Implantable medical devices and coatings therefor comprising physically crosslinked block copolymers |
US7757543B2 (en) | 2006-07-13 | 2010-07-20 | Advanced Cardiovascular Systems, Inc. | Radio frequency identification monitoring of stents |
US7998404B2 (en) * | 2006-07-13 | 2011-08-16 | Advanced Cardiovascular Systems, Inc. | Reduced temperature sterilization of stents |
US7794495B2 (en) * | 2006-07-17 | 2010-09-14 | Advanced Cardiovascular Systems, Inc. | Controlled degradation of stents |
US7559137B2 (en) * | 2006-07-17 | 2009-07-14 | Potomac Photonics, Inc. | Method for providing electrically conductive paths in polymer tubing |
US7886419B2 (en) * | 2006-07-18 | 2011-02-15 | Advanced Cardiovascular Systems, Inc. | Stent crimping apparatus and method |
US8016879B2 (en) * | 2006-08-01 | 2011-09-13 | Abbott Cardiovascular Systems Inc. | Drug delivery after biodegradation of the stent scaffolding |
US20080091262A1 (en) * | 2006-10-17 | 2008-04-17 | Gale David C | Drug delivery after biodegradation of the stent scaffolding |
WO2008017028A2 (en) | 2006-08-02 | 2008-02-07 | Boston Scientific Scimed, Inc. | Endoprosthesis with three-dimensional disintegration control |
US9173733B1 (en) | 2006-08-21 | 2015-11-03 | Abbott Cardiovascular Systems Inc. | Tracheobronchial implantable medical device and methods of use |
US7857008B2 (en) * | 2006-08-24 | 2010-12-28 | Boston Scientific Scimed, Inc. | Medical device coating configuration and method for improved lubricity and durability |
US7923022B2 (en) * | 2006-09-13 | 2011-04-12 | Advanced Cardiovascular Systems, Inc. | Degradable polymeric implantable medical devices with continuous phase and discrete phase |
WO2008033711A2 (en) | 2006-09-14 | 2008-03-20 | Boston Scientific Limited | Medical devices with drug-eluting coating |
ES2368125T3 (en) | 2006-09-15 | 2011-11-14 | Boston Scientific Scimed, Inc. | BIOEROSIONABLE ENDOPROOTHESIS WITH BIOESTABLE INORGANIC LAYERS. |
WO2008034047A2 (en) | 2006-09-15 | 2008-03-20 | Boston Scientific Limited | Endoprosthesis with adjustable surface features |
JP2010503485A (en) | 2006-09-15 | 2010-02-04 | ボストン サイエンティフィック リミテッド | Medical device and method for manufacturing the same |
JP2010503489A (en) | 2006-09-15 | 2010-02-04 | ボストン サイエンティフィック リミテッド | Biodegradable endoprosthesis and method for producing the same |
US8057534B2 (en) | 2006-09-15 | 2011-11-15 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
CA2663762A1 (en) | 2006-09-18 | 2008-03-27 | Boston Scientific Limited | Endoprostheses |
US7963942B2 (en) * | 2006-09-20 | 2011-06-21 | Boston Scientific Scimed, Inc. | Medical balloons with modified surfaces |
US20080069858A1 (en) | 2006-09-20 | 2008-03-20 | Boston Scientific Scimed, Inc. | Medical devices having biodegradable polymeric regions with overlying hard, thin layers |
JP2009297719A (en) * | 2006-10-02 | 2009-12-24 | Hikari Physics Kenkyusho:Kk | Laser working apparatus and method for capillary |
US20080097588A1 (en) | 2006-10-18 | 2008-04-24 | Conor Medsystems, Inc. | Systems and Methods for Producing a Medical Device |
EP2086600B1 (en) * | 2006-11-03 | 2016-10-26 | Boston Scientific Limited | Stents with drug eluting coatings |
US7981150B2 (en) * | 2006-11-09 | 2011-07-19 | Boston Scientific Scimed, Inc. | Endoprosthesis with coatings |
US9040816B2 (en) * | 2006-12-08 | 2015-05-26 | Nanocopoeia, Inc. | Methods and apparatus for forming photovoltaic cells using electrospray |
US8099849B2 (en) | 2006-12-13 | 2012-01-24 | Abbott Cardiovascular Systems Inc. | Optimizing fracture toughness of polymeric stent |
EP2277563B1 (en) | 2006-12-28 | 2014-06-25 | Boston Scientific Limited | Bioerodible endoprostheses and method of making the same |
US8114466B2 (en) * | 2007-01-03 | 2012-02-14 | Boston Scientific Scimed, Inc. | Methods of applying coating to the inside surface of a stent |
US8187255B2 (en) * | 2007-02-02 | 2012-05-29 | Boston Scientific Scimed, Inc. | Medical devices having nanoporous coatings for controlled therapeutic agent delivery |
US8431149B2 (en) | 2007-03-01 | 2013-04-30 | Boston Scientific Scimed, Inc. | Coated medical devices for abluminal drug delivery |
US8070797B2 (en) | 2007-03-01 | 2011-12-06 | Boston Scientific Scimed, Inc. | Medical device with a porous surface for delivery of a therapeutic agent |
US20080243228A1 (en) * | 2007-03-28 | 2008-10-02 | Yunbing Wang | Implantable medical devices fabricated from block copolymers |
US8067054B2 (en) * | 2007-04-05 | 2011-11-29 | Boston Scientific Scimed, Inc. | Stents with ceramic drug reservoir layer and methods of making and using the same |
US8262723B2 (en) | 2007-04-09 | 2012-09-11 | Abbott Cardiovascular Systems Inc. | Implantable medical devices fabricated from polymer blends with star-block copolymers |
US7976915B2 (en) | 2007-05-23 | 2011-07-12 | Boston Scientific Scimed, Inc. | Endoprosthesis with select ceramic morphology |
US7829008B2 (en) * | 2007-05-30 | 2010-11-09 | Abbott Cardiovascular Systems Inc. | Fabricating a stent from a blow molded tube |
US7959857B2 (en) * | 2007-06-01 | 2011-06-14 | Abbott Cardiovascular Systems Inc. | Radiation sterilization of medical devices |
US8293260B2 (en) * | 2007-06-05 | 2012-10-23 | Abbott Cardiovascular Systems Inc. | Elastomeric copolymer coatings containing poly (tetramethyl carbonate) for implantable medical devices |
US8202528B2 (en) * | 2007-06-05 | 2012-06-19 | Abbott Cardiovascular Systems Inc. | Implantable medical devices with elastomeric block copolymer coatings |
US20080306582A1 (en) * | 2007-06-05 | 2008-12-11 | Yunbing Wang | Implantable medical devices with elastomeric copolymer coatings |
US8425591B1 (en) | 2007-06-11 | 2013-04-23 | Abbott Cardiovascular Systems Inc. | Methods of forming polymer-bioceramic composite medical devices with bioceramic particles |
US8048441B2 (en) | 2007-06-25 | 2011-11-01 | Abbott Cardiovascular Systems, Inc. | Nanobead releasing medical devices |
US7901452B2 (en) * | 2007-06-27 | 2011-03-08 | Abbott Cardiovascular Systems Inc. | Method to fabricate a stent having selected morphology to reduce restenosis |
US7955381B1 (en) | 2007-06-29 | 2011-06-07 | Advanced Cardiovascular Systems, Inc. | Polymer-bioceramic composite implantable medical device with different types of bioceramic particles |
US7942926B2 (en) * | 2007-07-11 | 2011-05-17 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US8002823B2 (en) | 2007-07-11 | 2011-08-23 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
JP2010533563A (en) | 2007-07-19 | 2010-10-28 | ボストン サイエンティフィック リミテッド | Endoprosthesis with adsorption inhibiting surface |
US7931683B2 (en) | 2007-07-27 | 2011-04-26 | Boston Scientific Scimed, Inc. | Articles having ceramic coated surfaces |
US8815273B2 (en) | 2007-07-27 | 2014-08-26 | Boston Scientific Scimed, Inc. | Drug eluting medical devices having porous layers |
US8221822B2 (en) | 2007-07-31 | 2012-07-17 | Boston Scientific Scimed, Inc. | Medical device coating by laser cladding |
JP2010535541A (en) | 2007-08-03 | 2010-11-25 | ボストン サイエンティフィック リミテッド | Coating for medical devices with large surface area |
US8052745B2 (en) | 2007-09-13 | 2011-11-08 | Boston Scientific Scimed, Inc. | Endoprosthesis |
US9034007B2 (en) | 2007-09-21 | 2015-05-19 | Insera Therapeutics, Inc. | Distal embolic protection devices with a variable thickness microguidewire and methods for their use |
US20090081272A1 (en) * | 2007-09-24 | 2009-03-26 | John Clarke | Medical devices having a metal particulate composition for controlled diffusion |
US8974809B2 (en) * | 2007-09-24 | 2015-03-10 | Boston Scientific Scimed, Inc. | Medical devices having a filter insert for controlled diffusion |
US20090118813A1 (en) * | 2007-11-02 | 2009-05-07 | Torsten Scheuermann | Nano-patterned implant surfaces |
US8029554B2 (en) | 2007-11-02 | 2011-10-04 | Boston Scientific Scimed, Inc. | Stent with embedded material |
US7938855B2 (en) | 2007-11-02 | 2011-05-10 | Boston Scientific Scimed, Inc. | Deformable underlayer for stent |
US8216632B2 (en) | 2007-11-02 | 2012-07-10 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
WO2009076592A2 (en) * | 2007-12-12 | 2009-06-18 | Boston Scientific Scimed, Inc. | Medical devices having porous component for controlled diffusion |
DE102007062182A1 (en) * | 2007-12-21 | 2009-06-25 | Robert Bosch Gmbh | Injection valve for injecting fuel, into mixture processing apparatus in fuel injection or exhaust system of internal-combustion engine, has blowhole formed in ceramic body using laser which transmits pulses with extremely small pulse time |
CA2711001A1 (en) * | 2007-12-26 | 2009-07-09 | Gel-Del Technologies, Inc. | Biocompatible protein-based particles and methods thereof |
JP5581311B2 (en) | 2008-04-22 | 2014-08-27 | ボストン サイエンティフィック サイムド,インコーポレイテッド | MEDICAL DEVICE HAVING INORGANIC MATERIAL COATING AND MANUFACTURING METHOD THEREOF |
WO2009132176A2 (en) | 2008-04-24 | 2009-10-29 | Boston Scientific Scimed, Inc. | Medical devices having inorganic particle layers |
US7998192B2 (en) | 2008-05-09 | 2011-08-16 | Boston Scientific Scimed, Inc. | Endoprostheses |
US8236046B2 (en) | 2008-06-10 | 2012-08-07 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis |
WO2009155328A2 (en) | 2008-06-18 | 2009-12-23 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US20090319026A1 (en) * | 2008-06-20 | 2009-12-24 | Boston Scientific Scimed, Inc. | Composite Stent with Reservoirs for Drug Delivery and Methods of Manufacturing |
EP2149414A1 (en) | 2008-07-30 | 2010-02-03 | Nederlandse Centrale Organisatie Voor Toegepast Natuurwetenschappelijk Onderzoek TNO | Method of manufacturing a porous magnesium, or magnesium alloy, biomedical implant or medical appliance. |
US7985252B2 (en) | 2008-07-30 | 2011-07-26 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis |
US8226603B2 (en) * | 2008-09-25 | 2012-07-24 | Abbott Cardiovascular Systems Inc. | Expandable member having a covering formed of a fibrous matrix for intraluminal drug delivery |
US8049061B2 (en) | 2008-09-25 | 2011-11-01 | Abbott Cardiovascular Systems, Inc. | Expandable member formed of a fibrous matrix having hydrogel polymer for intraluminal drug delivery |
US8076529B2 (en) * | 2008-09-26 | 2011-12-13 | Abbott Cardiovascular Systems, Inc. | Expandable member formed of a fibrous matrix for intraluminal drug delivery |
US8500687B2 (en) | 2008-09-25 | 2013-08-06 | Abbott Cardiovascular Systems Inc. | Stent delivery system having a fibrous matrix covering with improved stent retention |
US8382824B2 (en) | 2008-10-03 | 2013-02-26 | Boston Scientific Scimed, Inc. | Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides |
WO2010057177A2 (en) | 2008-11-17 | 2010-05-20 | Gel-Del Technologies, Inc. | Protein biomaterial and biocoacervate vessel graft systems and methods of making and using thereof |
US8231980B2 (en) | 2008-12-03 | 2012-07-31 | Boston Scientific Scimed, Inc. | Medical implants including iridium oxide |
US8461478B2 (en) | 2009-02-03 | 2013-06-11 | Abbott Cardiovascular Systems, Inc. | Multiple beam laser system for forming stents |
EP2393628B1 (en) * | 2009-02-03 | 2017-06-21 | Abbott Cardiovascular Systems Inc. | Improved laser cutting system |
WO2010091093A1 (en) * | 2009-02-03 | 2010-08-12 | Abbott Cardiovascular Systems Inc. | Improved laser cutting process for forming stents |
US8267992B2 (en) | 2009-03-02 | 2012-09-18 | Boston Scientific Scimed, Inc. | Self-buffering medical implants |
US8071156B2 (en) | 2009-03-04 | 2011-12-06 | Boston Scientific Scimed, Inc. | Endoprostheses |
US8287937B2 (en) | 2009-04-24 | 2012-10-16 | Boston Scientific Scimed, Inc. | Endoprosthese |
US20100285085A1 (en) * | 2009-05-07 | 2010-11-11 | Abbott Cardiovascular Systems Inc. | Balloon coating with drug transfer control via coating thickness |
CA2761579C (en) * | 2009-05-29 | 2014-08-19 | Medovent Gmbh | A medical product comprising a chitosan-coated wall and a method for manufacturing a medical product |
SG178565A1 (en) | 2009-08-28 | 2012-04-27 | Sernova Corp | Methods and devices for cellular transplantation |
US20110066223A1 (en) * | 2009-09-14 | 2011-03-17 | Hossainy Syed F A | Bioabsorbable Stent With Time Dependent Structure And Properties |
US8425587B2 (en) * | 2009-09-17 | 2013-04-23 | Abbott Cardiovascular Systems Inc. | Method of treatment with a bioabsorbable stent with time dependent structure and properties and regio-selective degradation |
US20110178592A1 (en) * | 2009-09-29 | 2011-07-21 | M.I.Tech Co., Inc. | Implantable Tube And Coating Method Thereof |
EP2338534A2 (en) * | 2009-12-21 | 2011-06-29 | Biotronik VI Patent AG | Medical implant, coating method and implantation method |
US8568471B2 (en) | 2010-01-30 | 2013-10-29 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer scaffolds |
US8808353B2 (en) | 2010-01-30 | 2014-08-19 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer scaffolds having a low crossing profile |
WO2011119573A1 (en) | 2010-03-23 | 2011-09-29 | Boston Scientific Scimed, Inc. | Surface treated bioerodible metal endoprostheses |
EP2555811B1 (en) | 2010-04-06 | 2017-09-27 | Boston Scientific Scimed, Inc. | Endoprosthesis |
US8556511B2 (en) | 2010-09-08 | 2013-10-15 | Abbott Cardiovascular Systems, Inc. | Fluid bearing to support stent tubing during laser cutting |
US10406009B2 (en) | 2010-09-15 | 2019-09-10 | Abbott Cardiovascular Systems Inc. | Bioabsorbable superficial femoral stent patterns with designed to break links |
US8728563B2 (en) * | 2011-05-03 | 2014-05-20 | Palmaz Scientific, Inc. | Endoluminal implantable surfaces, stents, and grafts and method of making same |
US8726483B2 (en) | 2011-07-29 | 2014-05-20 | Abbott Cardiovascular Systems Inc. | Methods for uniform crimping and deployment of a polymer scaffold |
US9254212B2 (en) | 2012-04-06 | 2016-02-09 | Abbott Cardiovascular Systems Inc. | Segmented scaffolds and delivery thereof for peripheral applications |
DE102012010687B4 (en) | 2012-05-30 | 2021-08-19 | ADMEDES GmbH | A method for producing a body implant, an assembly comprising a guide wire and a body implant, and a medical instrument |
KR101489263B1 (en) | 2014-02-26 | 2015-02-04 | 썬텍 주식회사 | Method of manufacturing polymeric stent and polylactic acid polymeric stent |
US10010436B2 (en) | 2012-09-20 | 2018-07-03 | Dotter Intellectual Pte, Ltd. | Polymeric stent and methods of manufacturing the same |
DE102013113271B4 (en) * | 2012-12-17 | 2023-03-02 | Acandis Gmbh | Medical implant, treatment system with such an implant and method for producing an implant |
EP2968872B1 (en) | 2013-03-15 | 2019-09-25 | Insera Therapeutics, Inc. | Vascular treatment devices |
US8690907B1 (en) | 2013-03-15 | 2014-04-08 | Insera Therapeutics, Inc. | Vascular treatment methods |
US8715314B1 (en) | 2013-03-15 | 2014-05-06 | Insera Therapeutics, Inc. | Vascular treatment measurement methods |
US8679150B1 (en) | 2013-03-15 | 2014-03-25 | Insera Therapeutics, Inc. | Shape-set textile structure based mechanical thrombectomy methods |
CN104037063A (en) * | 2014-06-13 | 2014-09-10 | 京东方科技集团股份有限公司 | Film patterning method and film patterning device |
US20160144156A1 (en) * | 2014-11-20 | 2016-05-26 | Edwards Lifesciences Corporation | Inflatable device with etched modifications |
US9999527B2 (en) | 2015-02-11 | 2018-06-19 | Abbott Cardiovascular Systems Inc. | Scaffolds having radiopaque markers |
US9700443B2 (en) | 2015-06-12 | 2017-07-11 | Abbott Cardiovascular Systems Inc. | Methods for attaching a radiopaque marker to a scaffold |
JP2019508201A (en) | 2016-02-16 | 2019-03-28 | インセラ セラピューティクス,インク. | Suction device and fixed blood flow bypass device |
WO2020014411A1 (en) * | 2018-07-11 | 2020-01-16 | Pranav Soman | Hybrid additive-subtractive laser fabrication platform for shaping hydrogels |
Family Cites Families (27)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
SE445884B (en) | 1982-04-30 | 1986-07-28 | Medinvent Sa | DEVICE FOR IMPLANTATION OF A RODFORM PROTECTION |
US4733665C2 (en) | 1985-11-07 | 2002-01-29 | Expandable Grafts Partnership | Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft |
SE453258B (en) | 1986-04-21 | 1988-01-25 | Medinvent Sa | ELASTIC, SELF-EXPANDING PROTEST AND PROCEDURE FOR ITS MANUFACTURING |
US4800882A (en) | 1987-03-13 | 1989-01-31 | Cook Incorporated | Endovascular stent and delivery system |
US4886062A (en) | 1987-10-19 | 1989-12-12 | Medtronic, Inc. | Intravascular radially expandable stent and method of implant |
US5304121A (en) | 1990-12-28 | 1994-04-19 | Boston Scientific Corporation | Drug delivery system making use of a hydrogel polymer coating |
US5674192A (en) | 1990-12-28 | 1997-10-07 | Boston Scientific Corporation | Drug delivery |
US5120322A (en) | 1990-06-13 | 1992-06-09 | Lathrotec, Inc. | Method and apparatus for treatment of fibrotic lesions |
US5356433A (en) | 1991-08-13 | 1994-10-18 | Cordis Corporation | Biocompatible metal surfaces |
CA2380683C (en) * | 1991-10-28 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Expandable stents and method for making same |
US5336518A (en) | 1992-12-11 | 1994-08-09 | Cordis Corporation | Treatment of metallic surfaces using radiofrequency plasma deposition and chemical attachment of bioactive agents |
US5464650A (en) | 1993-04-26 | 1995-11-07 | Medtronic, Inc. | Intravascular stent and method |
DE69534640T2 (en) * | 1994-04-29 | 2006-08-10 | Scimed Life Systems, Inc., Maple Grove | Stent with collagen |
US5629077A (en) | 1994-06-27 | 1997-05-13 | Advanced Cardiovascular Systems, Inc. | Biodegradable mesh and film stent |
CA2301351C (en) * | 1994-11-28 | 2002-01-22 | Advanced Cardiovascular Systems, Inc. | Method and apparatus for direct laser cutting of metal stents |
US5609629A (en) | 1995-06-07 | 1997-03-11 | Med Institute, Inc. | Coated implantable medical device |
EP0866950B1 (en) * | 1995-12-15 | 2001-07-04 | Siemens Aktiengesellschaft | Air mass meter |
EP0842729A1 (en) | 1996-10-21 | 1998-05-20 | Arterial Vascular Engineering, Inc. | Method and apparatus for laser processing of intravascular devices |
US5879697A (en) | 1997-04-30 | 1999-03-09 | Schneider Usa Inc | Drug-releasing coatings for medical devices |
DE19739912C1 (en) * | 1997-09-11 | 1998-12-10 | Schott Glas | New alkali-free aluminoborosilicate glass |
DE19745294A1 (en) | 1997-10-14 | 1999-04-15 | Biotronik Mess & Therapieg | Process for the production of fine-structured medical technology implants |
US6264687B1 (en) | 1998-04-20 | 2001-07-24 | Cordis Corporation | Multi-laminate stent having superelastic articulated sections |
WO1999056663A2 (en) * | 1998-05-05 | 1999-11-11 | Scimed Life Systems, Inc. | Stent with smooth ends |
US6153252A (en) * | 1998-06-30 | 2000-11-28 | Ethicon, Inc. | Process for coating stents |
US6171327B1 (en) * | 1999-02-24 | 2001-01-09 | Scimed Life Systems, Inc. | Intravascular filter and method |
US6620192B1 (en) | 1999-03-16 | 2003-09-16 | Advanced Cardiovascular Systems, Inc. | Multilayer stent |
US6471721B1 (en) * | 1999-12-30 | 2002-10-29 | Advanced Cardiovascular Systems, Inc. | Vascular stent having increased radiopacity and method for making same |
-
2000
- 2000-11-28 US US09/724,503 patent/US6517888B1/en not_active Expired - Fee Related
-
2001
- 2001-11-27 CA CA002430126A patent/CA2430126A1/en not_active Abandoned
- 2001-11-27 AU AU2002236491A patent/AU2002236491B2/en not_active Ceased
- 2001-11-27 WO PCT/US2001/044301 patent/WO2002043619A2/en active IP Right Grant
- 2001-11-27 AU AU3649102A patent/AU3649102A/en active Pending
- 2001-11-27 JP JP2002545600A patent/JP2004520872A/en active Pending
- 2001-11-27 EP EP05021940A patent/EP1616535A1/en not_active Ceased
- 2001-11-27 DE DE60114044T patent/DE60114044T2/en not_active Expired - Fee Related
- 2001-11-27 EP EP01986023A patent/EP1341479B1/en not_active Expired - Lifetime
- 2001-12-03 US US10/004,954 patent/US20020065553A1/en not_active Abandoned
Also Published As
Publication number | Publication date |
---|---|
EP1341479B1 (en) | 2005-10-12 |
WO2002043619A3 (en) | 2003-02-13 |
JP2004520872A (en) | 2004-07-15 |
DE60114044D1 (en) | 2005-11-17 |
AU3649102A (en) | 2002-06-11 |
AU2002236491B2 (en) | 2006-08-17 |
EP1341479A2 (en) | 2003-09-10 |
DE60114044T2 (en) | 2006-05-11 |
US6517888B1 (en) | 2003-02-11 |
WO2002043619A2 (en) | 2002-06-06 |
US20020065553A1 (en) | 2002-05-30 |
EP1616535A1 (en) | 2006-01-18 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6517888B1 (en) | Method for manufacturing a medical device having a coated portion by laser ablation | |
AU2002236491A1 (en) | Method for manufacturing a medical device having a coated portion by laser ablation | |
US6764709B2 (en) | Method for making and measuring a coating on the surface of a medical device using an ultraviolet laser | |
US7291165B2 (en) | Medical device for delivering biologically active material | |
US20050266039A1 (en) | Coated medical device and method for making the same | |
US20050196518A1 (en) | Method and system for making a coated medical device | |
US7326245B2 (en) | Medical device for delivering biologically active material | |
AU2003273359B2 (en) | Method of applying coatings to a medical device | |
US20070239253A1 (en) | Oscillation assisted drug elution apparatus and method | |
US20050203606A1 (en) | Stent system for preventing restenosis | |
US20050230039A1 (en) | Stent with protective pads or bulges | |
US20100102046A1 (en) | Laser Machining Medical Devices With Localized Cooling | |
US20080206441A1 (en) | Ion Beam Etching a Surface of an Implantable Medical Device | |
US20100106242A1 (en) | Stent and method for making a stent |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
EEER | Examination request | ||
FZDE | Discontinued | ||
FZDE | Discontinued |
Effective date: 20091127 |