CA2370824A1 - Medical device coating methods and devices - Google Patents
Medical device coating methods and devices Download PDFInfo
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- CA2370824A1 CA2370824A1 CA002370824A CA2370824A CA2370824A1 CA 2370824 A1 CA2370824 A1 CA 2370824A1 CA 002370824 A CA002370824 A CA 002370824A CA 2370824 A CA2370824 A CA 2370824A CA 2370824 A1 CA2370824 A1 CA 2370824A1
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- stmt
- medical device
- coating
- tool
- polymeric material
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B05—SPRAYING OR ATOMISING IN GENERAL; APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
- B05D—PROCESSES FOR APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
- B05D3/00—Pretreatment of surfaces to which liquids or other fluent materials are to be applied; After-treatment of applied coatings, e.g. intermediate treating of an applied coating preparatory to subsequent applications of liquids or other fluent materials
- B05D3/04—Pretreatment of surfaces to which liquids or other fluent materials are to be applied; After-treatment of applied coatings, e.g. intermediate treating of an applied coating preparatory to subsequent applications of liquids or other fluent materials by exposure to gases
- B05D3/0406—Pretreatment of surfaces to which liquids or other fluent materials are to be applied; After-treatment of applied coatings, e.g. intermediate treating of an applied coating preparatory to subsequent applications of liquids or other fluent materials by exposure to gases the gas being air
- B05D3/042—Directing or stopping the fluid to be coated with air
-
- 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
- A61F2/01—Filters implantable into blood vessels
- A61F2/0105—Open ended, i.e. legs gathered only at one side
-
- 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
- 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
- A61F2/915—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 with bands having a meander structure, adjacent bands being connected to each other
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/08—Materials for coatings
- A61L31/10—Macromolecular materials
-
- 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
- A61L31/16—Biologically active materials, e.g. therapeutic substances
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B05—SPRAYING OR ATOMISING IN GENERAL; APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
- B05C—APPARATUS FOR APPLYING FLUENT MATERIALS TO SURFACES, IN GENERAL
- B05C11/00—Component parts, details or accessories not specifically provided for in groups B05C1/00 - B05C9/00
- B05C11/02—Apparatus for spreading or distributing liquids or other fluent materials already applied to a surface ; Controlling means therefor; Control of the thickness of a coating by spreading or distributing liquids or other fluent materials already applied to the coated surface
- B05C11/06—Apparatus for spreading or distributing liquids or other fluent materials already applied to a surface ; Controlling means therefor; Control of the thickness of a coating by spreading or distributing liquids or other fluent materials already applied to the coated surface with a blast of gas or vapour
-
- 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
- A61F2/915—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 with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/91533—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 with bands having a meander structure, adjacent bands being connected to each other characterised by the phase between adjacent bands
- A61F2002/91541—Adjacent bands are arranged out of phase
-
- 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
- A61F2/915—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 with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/9155—Adjacent bands being connected to each other
- A61F2002/91558—Adjacent bands being connected to each other connected peak to peak
-
- 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
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0008—Fixation appliances for connecting prostheses to the body
- A61F2220/0016—Fixation appliances for connecting prostheses to the body with sharp anchoring protrusions, e.g. barbs, pins, spikes
-
- 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
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0004—Rounded shapes, e.g. with rounded corners
- A61F2230/0006—Rounded shapes, e.g. with rounded corners circular
-
- 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
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0028—Shapes in the form of latin or greek characters
- A61F2230/005—Rosette-shaped, e.g. star-shaped
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0028—Shapes in the form of latin or greek characters
- A61F2230/0054—V-shaped
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- 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
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0063—Three-dimensional shapes
- A61F2230/0067—Three-dimensional shapes conical
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/60—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
- A61L2300/606—Coatings
Abstract
Devices and methods for applying a polymeric coating to a medical device. The steps of the coating process including applying a liquid polymeric material to the surface of the medical device, then directing a stream of gas to impinge on the surface of the medical device. Excess liquid polymeric material is removed from the surface of the medical device. The devices used in the coating process and the coated medical device are also part of this invention.
Description
MEDICAL DEVICE COATING METHODS AND DEVICES
Field of the Invention The present invention relates generally to a medical device having a surface treatment applied over a portion of its surface. More particularly, the present invention relates to implantable medical devices having drug release coatings including a therapeutic substance in a polymeric carrier.
Background of the Invention There are a number of medical conditions which may be effectively treated with implantable medical devices. In many cases, the therapeutic effect of the 1o implantable medical device may be enhanced, if the device includes a drug release coating including a therapeutic substance in a polymeric Garner. Two examples of implantable medical devices which may include such drug release coatings are endovascular stems and vascular filters.
Intravascular diseases are commonly treated by relatively non-invasive techniques such as percutaneous transluminal angioplasty (PTA) and percutaneous transluminal coronary angioplasty (PTCA). These angioplasty techniques typically involve the use of a guidewire and a balloon catheter. In these procedures, a balloon catheter is advanced over a guidewire such that the balloon is positioned proximate a restriction in a diseased vessel. The balloon is then inflated and the restriction in the 2o vessel is opened.
While angioplasty techniques have gained wide acceptance, abrupt closure and restenosis have been identified as possible subsequent occurrences. Abrupt closure refers to the acute occlusion of a vessel immediately after or within the initial hours following a dilation procedure. Abrupt closure can result in myocardial infarction if blood flow is not restored in a timely manner. The primary mechanisms of abrupt closures are arterial dissection and/or thrombosis. Restenosis refers to the re-narrowing of an artery after an initially successful angioplasty. Restenosis occurs primarily within the initial six months after angioplasty, and is believed due to the proliferation and migration of the cellular components of the arterial wall.
Endovascular stems are placed in the dilated segment of a vessel lumen to mechanically block the effects of abrupt closure and restenosis. Such a stmt is disclosed in U.S. Patent No. 5,514,154 to Lau et al.
Recent developments have led to stems which can provide anti-thrombogenic and other medications to regions of a blood vessel which have been treated by angioplasty or other interventional techniques. In U.S. Patent No. 5,464,650, Berg et al. disclose a method for making an intravascular stmt by applying to the stmt, and in particular to its tissue-contacting surface, a solution which includes a solvent, a polymer dissolved in the solvent, and a therapeutic substance dispersed in the solvent.
After the solution is applied to the stmt, the solvent is evaporated leaving the polymer/therapeutic agent surface treatment. Berg et al. assert that these devices are capable of providing both short term medication delivery, over the initial hours and 1 o days after treatment, as well as long term medication delivery, over the weeks and months after treatment.
The process disclosed by Berg et al., which uses a polymeric carrier, is prone to the formation of polymeric surface imperfections during the coating process. This is especially evident on stems, which generally include many wire like members with interstitial spaces therebetween. The surface imperfections can include strands of drug laden polymeric material hanging loosely from or extending across the interstitial spaces in the stmt. The imperfections can also include chunks or thickened coating portions at particular points relative to the rest of the coating.
These imperfections, because of their drug delivering capabilities, may cause adverse 2o effects. Loose strands or strands across interstitial spaces may not be secure, and thus, may enter the blood stream and fail to provide local treatment. If these agents are released to locations other than the targeted area, unwanted side effects may result. An uneven coating may also result in non-uniform treatment of the vessel wall.
As mentioned previously, vascular filters are another type of implantable medical device which may benefit from the inclusion of a drug release coating including a therapeutic substance in a polymeric carrier. One of the most common applications for vascular filters is the treatment of Deep Venous Thrombosis (DVT).
Deep Venous Thrombosis patients experience clotting of blood in the large veins of 3o the lower portions of the body. These patients are constantly at risk of a clot breaking free and traveling via the inferior vena cava to the heart and lungs. This process is known as pulmonary embolization. Pulmonary embolization can frequently be fatal, because large blood clots can interfere with the function of the heart and/or lungs. For
Field of the Invention The present invention relates generally to a medical device having a surface treatment applied over a portion of its surface. More particularly, the present invention relates to implantable medical devices having drug release coatings including a therapeutic substance in a polymeric carrier.
Background of the Invention There are a number of medical conditions which may be effectively treated with implantable medical devices. In many cases, the therapeutic effect of the 1o implantable medical device may be enhanced, if the device includes a drug release coating including a therapeutic substance in a polymeric Garner. Two examples of implantable medical devices which may include such drug release coatings are endovascular stems and vascular filters.
Intravascular diseases are commonly treated by relatively non-invasive techniques such as percutaneous transluminal angioplasty (PTA) and percutaneous transluminal coronary angioplasty (PTCA). These angioplasty techniques typically involve the use of a guidewire and a balloon catheter. In these procedures, a balloon catheter is advanced over a guidewire such that the balloon is positioned proximate a restriction in a diseased vessel. The balloon is then inflated and the restriction in the 2o vessel is opened.
While angioplasty techniques have gained wide acceptance, abrupt closure and restenosis have been identified as possible subsequent occurrences. Abrupt closure refers to the acute occlusion of a vessel immediately after or within the initial hours following a dilation procedure. Abrupt closure can result in myocardial infarction if blood flow is not restored in a timely manner. The primary mechanisms of abrupt closures are arterial dissection and/or thrombosis. Restenosis refers to the re-narrowing of an artery after an initially successful angioplasty. Restenosis occurs primarily within the initial six months after angioplasty, and is believed due to the proliferation and migration of the cellular components of the arterial wall.
Endovascular stems are placed in the dilated segment of a vessel lumen to mechanically block the effects of abrupt closure and restenosis. Such a stmt is disclosed in U.S. Patent No. 5,514,154 to Lau et al.
Recent developments have led to stems which can provide anti-thrombogenic and other medications to regions of a blood vessel which have been treated by angioplasty or other interventional techniques. In U.S. Patent No. 5,464,650, Berg et al. disclose a method for making an intravascular stmt by applying to the stmt, and in particular to its tissue-contacting surface, a solution which includes a solvent, a polymer dissolved in the solvent, and a therapeutic substance dispersed in the solvent.
After the solution is applied to the stmt, the solvent is evaporated leaving the polymer/therapeutic agent surface treatment. Berg et al. assert that these devices are capable of providing both short term medication delivery, over the initial hours and 1 o days after treatment, as well as long term medication delivery, over the weeks and months after treatment.
The process disclosed by Berg et al., which uses a polymeric carrier, is prone to the formation of polymeric surface imperfections during the coating process. This is especially evident on stems, which generally include many wire like members with interstitial spaces therebetween. The surface imperfections can include strands of drug laden polymeric material hanging loosely from or extending across the interstitial spaces in the stmt. The imperfections can also include chunks or thickened coating portions at particular points relative to the rest of the coating.
These imperfections, because of their drug delivering capabilities, may cause adverse 2o effects. Loose strands or strands across interstitial spaces may not be secure, and thus, may enter the blood stream and fail to provide local treatment. If these agents are released to locations other than the targeted area, unwanted side effects may result. An uneven coating may also result in non-uniform treatment of the vessel wall.
As mentioned previously, vascular filters are another type of implantable medical device which may benefit from the inclusion of a drug release coating including a therapeutic substance in a polymeric carrier. One of the most common applications for vascular filters is the treatment of Deep Venous Thrombosis (DVT).
Deep Venous Thrombosis patients experience clotting of blood in the large veins of 3o the lower portions of the body. These patients are constantly at risk of a clot breaking free and traveling via the inferior vena cava to the heart and lungs. This process is known as pulmonary embolization. Pulmonary embolization can frequently be fatal, because large blood clots can interfere with the function of the heart and/or lungs. For
2 example, a large blood clot which becomes trapped proximate the heart may interfere with the life-sustaining pumping action of the heart. A blood clot which passes through the heart will be pumped into the lungs and may cause a blockage in the pulmonary arteries. A blockage of this type in the lungs will interfere with the oxygenation of the blood causing shock or death.
Pulmonary embolization may be successfully prevented by the appropriate placement of a vascular filter in the vascular system of a patient's body.
Placement of the filter may be accomplished by performing a laparotomy with the patient under general anesthesia. However, intravenous insertion is often the preferred method of to placing a vascular in a patient's vascular system.
In the treatment of Deep Venous Thrombosis, a vascular filter is placed in the inferior vena cava of a patient. The inferior vena cava is a large vessel which returns blood to the heart from the lower part of the body. The inferior vena cava may be accessed through the patient's femoral vein.
Vascular filters may be placed in other locations when treating other conditions. For example, if blood clots are expected to approach the heart and lungs from the upper portion of the body, a vascular filter may be positioned in the superior vena cava. The superior vena cava is a large vessel which returns blood to the heart from the upper part of the body. The superior vena cava may by accessed through the 2o jugular vein, located in the patient's neck. Once placed inside a blood vessel, a vascular filter acts to catch and hold blood clots. The flow of blood around the captured clots allows the body's lysing process to dissolve the clots.
Summary of the Invention The present invention pertains to implantable medical devices having drug release coatings including a therapeutic substance in a polymer carrier. The present invention provides a method of applying a coating to an implantable medical device which is evenly distributed over all of the surfaces of the device. Two examples of implantable medical devices which may be coated using this process are stems and thrombosis filters. This method of coating may also be used with other implantable 3o medical devices. Also, this coating method may be used with stems of both self expanding and balloon expandable designs.
Stems are normally comprised of a skeletal frame which includes openings and a lumen which extends longitudinally through the stmt. A variety of processes
Pulmonary embolization may be successfully prevented by the appropriate placement of a vascular filter in the vascular system of a patient's body.
Placement of the filter may be accomplished by performing a laparotomy with the patient under general anesthesia. However, intravenous insertion is often the preferred method of to placing a vascular in a patient's vascular system.
In the treatment of Deep Venous Thrombosis, a vascular filter is placed in the inferior vena cava of a patient. The inferior vena cava is a large vessel which returns blood to the heart from the lower part of the body. The inferior vena cava may be accessed through the patient's femoral vein.
Vascular filters may be placed in other locations when treating other conditions. For example, if blood clots are expected to approach the heart and lungs from the upper portion of the body, a vascular filter may be positioned in the superior vena cava. The superior vena cava is a large vessel which returns blood to the heart from the upper part of the body. The superior vena cava may by accessed through the 2o jugular vein, located in the patient's neck. Once placed inside a blood vessel, a vascular filter acts to catch and hold blood clots. The flow of blood around the captured clots allows the body's lysing process to dissolve the clots.
Summary of the Invention The present invention pertains to implantable medical devices having drug release coatings including a therapeutic substance in a polymer carrier. The present invention provides a method of applying a coating to an implantable medical device which is evenly distributed over all of the surfaces of the device. Two examples of implantable medical devices which may be coated using this process are stems and thrombosis filters. This method of coating may also be used with other implantable 3o medical devices. Also, this coating method may be used with stems of both self expanding and balloon expandable designs.
Stems are normally comprised of a skeletal frame which includes openings and a lumen which extends longitudinally through the stmt. A variety of processes
3 are known for fabricating stems. A stmt may consist of a plurality of filaments or fibers which are wound or braided together to form a continuous structure.
Alternately, the skeletal frame of a stmt may be formed by removing material from a tubular element using a laser cutting process. A stmt may be comprised of any biocompatible material possessing the structural and mechanical attributes necessary for supporting a diseased vessel.
Often, it is beneficial to both stmt and treat a localized area of a diseased vessel. A therapeutic agent, therefore, can be incorporated into a polymer and applied to the stmt as a polymeric surface treatment. Incorporation of a therapeutic agent into 1o a surface treatment greatly enhances the scope of this medical device by transforming the stmt into a drug delivery system. Drugs and treatments which utilize anti-thrombogenic agents, anti-angiogenisis agent, anti-proliferative agents, growth factors and radio chemicals may be readily deployed from within the matrix of the polymer surface treatment.
The application of such a surface treatment is generally accomplished by applying a coating solution to the stmt. Typically, this coating solution includes a solvent, a polymer dissolved in the solvent and a therapeutic substance dispersed in the solvent. The coating solution may be applied to the stmt using a variety of methods. For example, the solution may be applied to the stmt by immersing the 2o stmt in liquid coating solution. Alternately, the coating solution may be applied to the stmt with a brush. Finally, in a preferred embodiment, the coating solution may be sprayed onto the stmt.
Solvent selection is critical to a functioning surface treatment. It is essential that the solvent is capable of placing the polymer into solution and that the solvent and polymer chosen do not materially alter the therapeutic character of the therapeutic agent. On the other hand, the therapeutic agent needs only to be dispersed throughout the solvent. The therapeutic agent, therefore, may be either in a true solution with the solvent or dispersed in fine particles within the solvent.
It is preferred that the polymeric coating be evenly distributed over the stmt.
3o Although the procedures for applying a polymeric surface treatments are optimized, they still often leave polymeric fibers, polymeric particles, or other polymeric surface aberrations or imperfections on the stmt. These aberrations or imperfections in the polymeric coating may take on numerous sizes and shapes. Regardless of the
Alternately, the skeletal frame of a stmt may be formed by removing material from a tubular element using a laser cutting process. A stmt may be comprised of any biocompatible material possessing the structural and mechanical attributes necessary for supporting a diseased vessel.
Often, it is beneficial to both stmt and treat a localized area of a diseased vessel. A therapeutic agent, therefore, can be incorporated into a polymer and applied to the stmt as a polymeric surface treatment. Incorporation of a therapeutic agent into 1o a surface treatment greatly enhances the scope of this medical device by transforming the stmt into a drug delivery system. Drugs and treatments which utilize anti-thrombogenic agents, anti-angiogenisis agent, anti-proliferative agents, growth factors and radio chemicals may be readily deployed from within the matrix of the polymer surface treatment.
The application of such a surface treatment is generally accomplished by applying a coating solution to the stmt. Typically, this coating solution includes a solvent, a polymer dissolved in the solvent and a therapeutic substance dispersed in the solvent. The coating solution may be applied to the stmt using a variety of methods. For example, the solution may be applied to the stmt by immersing the 2o stmt in liquid coating solution. Alternately, the coating solution may be applied to the stmt with a brush. Finally, in a preferred embodiment, the coating solution may be sprayed onto the stmt.
Solvent selection is critical to a functioning surface treatment. It is essential that the solvent is capable of placing the polymer into solution and that the solvent and polymer chosen do not materially alter the therapeutic character of the therapeutic agent. On the other hand, the therapeutic agent needs only to be dispersed throughout the solvent. The therapeutic agent, therefore, may be either in a true solution with the solvent or dispersed in fine particles within the solvent.
It is preferred that the polymeric coating be evenly distributed over the stmt.
3o Although the procedures for applying a polymeric surface treatments are optimized, they still often leave polymeric fibers, polymeric particles, or other polymeric surface aberrations or imperfections on the stmt. These aberrations or imperfections in the polymeric coating may take on numerous sizes and shapes. Regardless of the
4 application process utilized, several types of imperfections are common.
Examples of these imperfections are polymeric fibers, which span across the openings of the skeletal framework of the stmt, and lumps created by an overabundance of polymeric material in a localized area. Imperfections in the polymeric coating may be a result of disproportionate application of the coating solution, or the settling of excessive material in a particular location. At a minimum, the imperfections are unsightly.
More importantly, imperfections may create adverse secondary effects.
The adverse secondary effects which may arise are correlated to the type of polymeric imperfections. Polymeric fibers are prone to two adverse effects;
the fibers 1o may dislodge from the stmt, or they may release their therapeutic agents into the blood stream. Because fibers span across openings in the skeletal framework of the stmt, they are attached typically at few locations. Expansion of the stmt may dislodge these imperfections sending them into the circulatory system. At this point, there exists no control over the drug delivery capabilities of these rogue fibers. The release of drugs in undesired locations is likely to cause secondary effects.
On the other hand, polymeric fibers may remain attached to the stmt. Some of the fibers which remain attached to the stmt may not engage the wall of the blood vessel.
In this instance, the entire surface of the polymeric fibers is free to release therapeutic agent directly into the blood stream, causing other secondary effects.
2o Polymeric lumps are caused by an overabundance of polymeric material in a localized area, these lumps may also cause secondary effects. As mentioned above, the goal of applying a polymeric surface treatment to a stmt is to have uniform coverage and uniform release of a therapeutic substance. When there are areas of excess coverage on the stmt, the targeted diseased tissue may receive a non-uniform dosage of the released therapeutic agent. For therapeutic agents, especially ones which promote or restrict endothelial cell growth, uneven release may cause non-optimal treatment. Another problem created by polymeric lumps is that the lumps may be in a location of the stmt where they do not contact the wall of the blood vessel. In this instance, the entire surface area of the lumps will be free to release 3o therapeutic agent directly into the blood stream, causing other secondary effects.
The present invention provides a method of applying an even coating to an implantable medical device either alone or in a combination with a therapeutic substance. The process begins with the step of preparing a coating solution preferably
Examples of these imperfections are polymeric fibers, which span across the openings of the skeletal framework of the stmt, and lumps created by an overabundance of polymeric material in a localized area. Imperfections in the polymeric coating may be a result of disproportionate application of the coating solution, or the settling of excessive material in a particular location. At a minimum, the imperfections are unsightly.
More importantly, imperfections may create adverse secondary effects.
The adverse secondary effects which may arise are correlated to the type of polymeric imperfections. Polymeric fibers are prone to two adverse effects;
the fibers 1o may dislodge from the stmt, or they may release their therapeutic agents into the blood stream. Because fibers span across openings in the skeletal framework of the stmt, they are attached typically at few locations. Expansion of the stmt may dislodge these imperfections sending them into the circulatory system. At this point, there exists no control over the drug delivery capabilities of these rogue fibers. The release of drugs in undesired locations is likely to cause secondary effects.
On the other hand, polymeric fibers may remain attached to the stmt. Some of the fibers which remain attached to the stmt may not engage the wall of the blood vessel.
In this instance, the entire surface of the polymeric fibers is free to release therapeutic agent directly into the blood stream, causing other secondary effects.
2o Polymeric lumps are caused by an overabundance of polymeric material in a localized area, these lumps may also cause secondary effects. As mentioned above, the goal of applying a polymeric surface treatment to a stmt is to have uniform coverage and uniform release of a therapeutic substance. When there are areas of excess coverage on the stmt, the targeted diseased tissue may receive a non-uniform dosage of the released therapeutic agent. For therapeutic agents, especially ones which promote or restrict endothelial cell growth, uneven release may cause non-optimal treatment. Another problem created by polymeric lumps is that the lumps may be in a location of the stmt where they do not contact the wall of the blood vessel. In this instance, the entire surface area of the lumps will be free to release 3o therapeutic agent directly into the blood stream, causing other secondary effects.
The present invention provides a method of applying an even coating to an implantable medical device either alone or in a combination with a therapeutic substance. The process begins with the step of preparing a coating solution preferably
5 including a polymer, a solvent, and a therapeutic substance. The coating solution is then applied to the stmt by dipping, spraying or any other acceptable method.
A tool or assembly as described herein is then used to direct a gas stream so that the gas stream impinges on the surfaces of the stmt. When the gas from the gas stream strikes the surfaces of the stmt, it displaces excess coating solution. The tool or assembly may be moved to direct the gas stream at the stmt from a plurality of different locations and from a plurality of different angles. The tool or assembly may also be in continuous rotational motion such that the gas streams generally impinge across the entire circumference of the stmt. The tool may be adapted so that it may 1 o be passed through the entire lumen of the stmt. The flow of gas through the openings and around the wires of the stmt is sufficient to displace excess coating solution, any lumps, fibers, etc. formed by the coating solution and will be blown off the surfaces of the stmt by the gas stream. Once the excess coating solution has been removed from the surfaces of the stmt, the solvent of the coating solution is allowed to evaporate, thereby leaving on the surface of the stmt, a polymer coating. As described above, the polymer coating ideally includes a therapeutic agent. Because all imperfections were removed before the coating solution was allowed to dry, the polymer coating which results from this process was evenly distributed across the surface of the stmt.
It should be understood that the coating method described above may be used 2o in conjunction with any stmt design. For example, this coating method may be used with both self expanding and balloon expandable stems. The coating method described above may also be used with implantable medical devices other than stems.
For example, a thrombosis filter may be coated using a coating method described above.
A typical thrombosis filter includes a body member and a plurality of elongated struts. Each strut has a free end and a joined end. The joined end of each strut is fixably attached to the body member. The struts radiate outwardly from the body member such that the thrombus filter is generally conical in shape. When the thrombosis is deployed inside a blood vessel, the free ends of the struts engage the 3o blood vessel wall. The body member of the thrombosis filter is held in a position proximate the center of the blood vessel by the plurality of struts which engage the blood vessel walls with opposing force vectors.
A tool or assembly as described herein is then used to direct a gas stream so that the gas stream impinges on the surfaces of the stmt. When the gas from the gas stream strikes the surfaces of the stmt, it displaces excess coating solution. The tool or assembly may be moved to direct the gas stream at the stmt from a plurality of different locations and from a plurality of different angles. The tool or assembly may also be in continuous rotational motion such that the gas streams generally impinge across the entire circumference of the stmt. The tool may be adapted so that it may 1 o be passed through the entire lumen of the stmt. The flow of gas through the openings and around the wires of the stmt is sufficient to displace excess coating solution, any lumps, fibers, etc. formed by the coating solution and will be blown off the surfaces of the stmt by the gas stream. Once the excess coating solution has been removed from the surfaces of the stmt, the solvent of the coating solution is allowed to evaporate, thereby leaving on the surface of the stmt, a polymer coating. As described above, the polymer coating ideally includes a therapeutic agent. Because all imperfections were removed before the coating solution was allowed to dry, the polymer coating which results from this process was evenly distributed across the surface of the stmt.
It should be understood that the coating method described above may be used 2o in conjunction with any stmt design. For example, this coating method may be used with both self expanding and balloon expandable stems. The coating method described above may also be used with implantable medical devices other than stems.
For example, a thrombosis filter may be coated using a coating method described above.
A typical thrombosis filter includes a body member and a plurality of elongated struts. Each strut has a free end and a joined end. The joined end of each strut is fixably attached to the body member. The struts radiate outwardly from the body member such that the thrombus filter is generally conical in shape. When the thrombosis is deployed inside a blood vessel, the free ends of the struts engage the 3o blood vessel wall. The body member of the thrombosis filter is held in a position proximate the center of the blood vessel by the plurality of struts which engage the blood vessel walls with opposing force vectors.
6 The walls of the blood vessel are lined with a thin inner membrane or intima.
When the free ends of the thrombus filter disrupt this inner membrane, the body responds in a process known as neointimal hyperplasia, or endothelial growth.
As a result of this process, the disrupted area of the inner membrane is overgrown with a number of new cells. The free ends of the thrombosis filter struts are encapsulated with new cell growth within 2-3 weeks of the implant of the filter.
Due to endothelial growth, thrombus filters placed in the blood vessel of a patient become affixed in the blood vessel walls within 2-3 weeks after being implanted. Because the free ends of the thrombus filter struts contacting the blood 1o vessel walls become fixed in this way, many thrombosis filters cannot be removed percutaneously after being in place for more than two weeks. Applying a polymer coating including a therapeutic substance in a polymer carrier to the free ends of a vascular filter struts may assist in preventing or reducing endothelial growth proximate the free ends of the struts.
When the thrombosis filter is disposed in a blood vessel, the conical formation of struts acts to trap or capture blood clots. The generally conical shape of the formation of struts serves to urge captured blood clots toward the center of the blood flow. The flow of blood around the captured blood clots allows the body's natural lysing process to dissolve the clots. Applying a polymer coating including a therapeutic substance in a polymeric carrier to the vascular filter may assist the body in dissolving blood clots.
The present invention provides a method which may be used to apply an evenly distributed polymeric coating to an implantable medical device such as a thrombus filter. The process begins with the step of preparing a coating solution preferably including a polymer, a solvent, and a therapeutic substance. The coating solution is then applied to selected surfaces of the thrombus filter. A tool or assembly is then used to direct gas streams so that they impinge on the surfaces of the thrombus filter. When the gas of the gas streams strikes the surfaces of the thrombus filter, it displaces excess coating solution. To assure that the gas streams impinge upon 3o substantially all of the surfaces of the thrombus filter, the tool may be rotated or moved in a linear direction. The tool or assembly may also be moved to a variety of positions. The flow of gas around the struts and body member of the thrombus filter is sufficient to displace excess coating solution. Once the excess coating solution has
When the free ends of the thrombus filter disrupt this inner membrane, the body responds in a process known as neointimal hyperplasia, or endothelial growth.
As a result of this process, the disrupted area of the inner membrane is overgrown with a number of new cells. The free ends of the thrombosis filter struts are encapsulated with new cell growth within 2-3 weeks of the implant of the filter.
Due to endothelial growth, thrombus filters placed in the blood vessel of a patient become affixed in the blood vessel walls within 2-3 weeks after being implanted. Because the free ends of the thrombus filter struts contacting the blood 1o vessel walls become fixed in this way, many thrombosis filters cannot be removed percutaneously after being in place for more than two weeks. Applying a polymer coating including a therapeutic substance in a polymer carrier to the free ends of a vascular filter struts may assist in preventing or reducing endothelial growth proximate the free ends of the struts.
When the thrombosis filter is disposed in a blood vessel, the conical formation of struts acts to trap or capture blood clots. The generally conical shape of the formation of struts serves to urge captured blood clots toward the center of the blood flow. The flow of blood around the captured blood clots allows the body's natural lysing process to dissolve the clots. Applying a polymer coating including a therapeutic substance in a polymeric carrier to the vascular filter may assist the body in dissolving blood clots.
The present invention provides a method which may be used to apply an evenly distributed polymeric coating to an implantable medical device such as a thrombus filter. The process begins with the step of preparing a coating solution preferably including a polymer, a solvent, and a therapeutic substance. The coating solution is then applied to selected surfaces of the thrombus filter. A tool or assembly is then used to direct gas streams so that they impinge on the surfaces of the thrombus filter. When the gas of the gas streams strikes the surfaces of the thrombus filter, it displaces excess coating solution. To assure that the gas streams impinge upon 3o substantially all of the surfaces of the thrombus filter, the tool may be rotated or moved in a linear direction. The tool or assembly may also be moved to a variety of positions. The flow of gas around the struts and body member of the thrombus filter is sufficient to displace excess coating solution. Once the excess coating solution has
7 been removed from the surfaces of the thrombosis filter, the solvent in the coating solution is allowed to evaporate thereby leaving on the surface of the thrombosis filter a polymer coating which preferably includes a therapeutic agent. Because all imperfections were removed before the solvent was allowed to evaporate, the polymer coating resulting from this process is evenly distributed across the surfaces of the thrombosis filter.
Brief Description of the Drawings Figure 1 is a perspective view of a stmt in accordance with an exemplary embodiment of the present invention;
to Figure 2 is a magnified, partial plan view of the stmt of Figure 1, illustrating the polymeric surface aberrations and imperfections arising from a polymeric coating procedure;
Figure 3 is a plan view of a stmt and an assembly to direct a gas stream at the stmt surface;
Figure 4 is a magnified, partial plan view of the stmt of Figure 1, illustrating an evenly applied polymeric coating applied using the coating and surface treating method of the present invention;
Figure 5 is a plan view of a stmt and an alternate assembly for directing a gas stream at the stmt surface ;
Figure 6 is a plan view of a stmt and another alternate assembly for directing a gas stream at the stmt surface;
Figure 7 is a plan view of a stmt and a further alternate assembly for directing a gas stream at the stmt surface; and Figure 8 is a perspective view of a thrombosis filter and an assembly for directing a gas stream at the filter surface.
Detailed Description of the Invention The following detailed description should be read with reference to the drawings, in which like elements in different drawings are numbered identically. The drawings which are not necessarily to scale, depict selected embodiments and are not 3o intended to limit the scope of the invention.
Examples of constructions, materials, dimensions, and manufacturing processes are provided for selected elements. All other elements employ that which is known to those of skill in the field of the invention. Those skilled in the art will
Brief Description of the Drawings Figure 1 is a perspective view of a stmt in accordance with an exemplary embodiment of the present invention;
to Figure 2 is a magnified, partial plan view of the stmt of Figure 1, illustrating the polymeric surface aberrations and imperfections arising from a polymeric coating procedure;
Figure 3 is a plan view of a stmt and an assembly to direct a gas stream at the stmt surface;
Figure 4 is a magnified, partial plan view of the stmt of Figure 1, illustrating an evenly applied polymeric coating applied using the coating and surface treating method of the present invention;
Figure 5 is a plan view of a stmt and an alternate assembly for directing a gas stream at the stmt surface ;
Figure 6 is a plan view of a stmt and another alternate assembly for directing a gas stream at the stmt surface;
Figure 7 is a plan view of a stmt and a further alternate assembly for directing a gas stream at the stmt surface; and Figure 8 is a perspective view of a thrombosis filter and an assembly for directing a gas stream at the filter surface.
Detailed Description of the Invention The following detailed description should be read with reference to the drawings, in which like elements in different drawings are numbered identically. The drawings which are not necessarily to scale, depict selected embodiments and are not 3o intended to limit the scope of the invention.
Examples of constructions, materials, dimensions, and manufacturing processes are provided for selected elements. All other elements employ that which is known to those of skill in the field of the invention. Those skilled in the art will
8
9 PCT/US00/11273 recognize that many of the examples provided have suitable alternatives which may be utilized.
Figure 1 is a perspective view of a stmt 10 having a skeletal frame 15.
Skeletal frame 15 of stmt 10 includes wire-like members or struts 12 forming a distinct, repetitive serpentine pattern. This repetitive serpentine pattern includes multiple U-shaped curves 14. Skeletal frame 15 also includes a plurality of openings or apertures 16. With no recognizable beginning or end to this serpentine pattern, each wire 12 forms an expandable serpentine element 18. Serpentine elements 18 are arranged along the longitudinal axis of stmt 10 so that abutting serpentine elements l0 18 may be joined together with additional wires 12. Skeletal frame 15 substantially forms a lumen 20 extending longitudinally through stmt 10.
The term "wire", as used in describing the material of skeletal frame 15 should not be mistaken as being limited to metallic materials. In fact, the "wire"
forming stmt 10 may be comprised of any biocompatible material possessing the structural and mechanical attributes necessary for supporting a diseased vessel. Thus, both metallic and non-metallic materials are suitable. Examples of preferred biocompatible metallic materials include stainless steel, tantalum, gold, titanium, and nickel-titanium alloy. Preferred non-metallic materials may be selected from the following list, which is not exhaustive: poly(L-lactide) (PLLA), poly(D,L-lactide) (PLA), polyglycolide (PGA), poly(L-lactide-co-D,L-lactide) (PLLA/PLA), poly(L-lactide-co-glycolide) (PLLA/PGA), poly(D, L-lactide-co-glycolide) (PLA/PGA), poly(glycolide-co-trimethylene carbonate) (PGA/PTMC), polyethylene oxide (PEO), polydioxanone (PDS), polycaprolactone (PCL), polyhydroxylbutyrate (PHBT), poly(phosphazene), polyp,L-lactide-co-caprolactone) (PLA/PCL), poly(glycolide-co-caprolactone) (PGA/PCL), polyanhydrides (PAN), poly(ortho esters), poly(phoshate ester), poly(amino acid), poly(hydroxy butyrate), polyacrylate, polyacrylamid, poly(hydroxyethyl methacrylate), polyurethane, polysiloxane and their copolymers.
Skeletal frame 15 of stmt 10 may be formed through various methods. For example, skeletal frame 15 may be assembled from a plurality of wires 12 joined 3o together by welding or soldering. Skeletal frame 15 may be molded in one piece using an injection molding process. Skeletal frame 15 may also be comprised of a plurality of filaments or fibers which are wound or braided together to form a continuous structure. Finally, in a preferred embodiment, skeletal frame 15 may be formed by removing material from a tubular element using a LASER cutting process.
Often it is beneficial to both stmt and treat a localized area of a diseased vessel. A therapeutic agent, therefore, can be incorporated into a polymer and applied to stmt 10 as a polymeric surface treatment. The incorporation of a therapeutic agent into a surface treatment greatly enhances the scope of this medical device by transforming the stmt into a drug-delivery system. Drugs and treatments which utilize anti-thrombogenic agents, anti-angiogenisis agents, anti-proliferative agents, growth factors, and radiochemicals may be readily deployed from within the matrix of to the polymeric surface treatment. Specific examples of preferred therapeutic agents include angiopeptin, colchicine, lovastatin, trapidil, ticlopidine, hirudin, Taxol, and heparin. Specific examples of growth factors which may serve as therapeutic agents include VEGF, TGF-beta, IGF, PDGF, and FGF.
The application of such a surface treatment is generally accomplished by applying a coating solution to stmt 10. Typically, this coating solution includes a solvent, a polymer dissolved in the solvent, and a therapeutic substance dispersed in the solvent. The coating solution may be applied to stmt 10 using a variety of methods. For example, the solution may be applied to stmt 10 by immersing stmt
Figure 1 is a perspective view of a stmt 10 having a skeletal frame 15.
Skeletal frame 15 of stmt 10 includes wire-like members or struts 12 forming a distinct, repetitive serpentine pattern. This repetitive serpentine pattern includes multiple U-shaped curves 14. Skeletal frame 15 also includes a plurality of openings or apertures 16. With no recognizable beginning or end to this serpentine pattern, each wire 12 forms an expandable serpentine element 18. Serpentine elements 18 are arranged along the longitudinal axis of stmt 10 so that abutting serpentine elements l0 18 may be joined together with additional wires 12. Skeletal frame 15 substantially forms a lumen 20 extending longitudinally through stmt 10.
The term "wire", as used in describing the material of skeletal frame 15 should not be mistaken as being limited to metallic materials. In fact, the "wire"
forming stmt 10 may be comprised of any biocompatible material possessing the structural and mechanical attributes necessary for supporting a diseased vessel. Thus, both metallic and non-metallic materials are suitable. Examples of preferred biocompatible metallic materials include stainless steel, tantalum, gold, titanium, and nickel-titanium alloy. Preferred non-metallic materials may be selected from the following list, which is not exhaustive: poly(L-lactide) (PLLA), poly(D,L-lactide) (PLA), polyglycolide (PGA), poly(L-lactide-co-D,L-lactide) (PLLA/PLA), poly(L-lactide-co-glycolide) (PLLA/PGA), poly(D, L-lactide-co-glycolide) (PLA/PGA), poly(glycolide-co-trimethylene carbonate) (PGA/PTMC), polyethylene oxide (PEO), polydioxanone (PDS), polycaprolactone (PCL), polyhydroxylbutyrate (PHBT), poly(phosphazene), polyp,L-lactide-co-caprolactone) (PLA/PCL), poly(glycolide-co-caprolactone) (PGA/PCL), polyanhydrides (PAN), poly(ortho esters), poly(phoshate ester), poly(amino acid), poly(hydroxy butyrate), polyacrylate, polyacrylamid, poly(hydroxyethyl methacrylate), polyurethane, polysiloxane and their copolymers.
Skeletal frame 15 of stmt 10 may be formed through various methods. For example, skeletal frame 15 may be assembled from a plurality of wires 12 joined 3o together by welding or soldering. Skeletal frame 15 may be molded in one piece using an injection molding process. Skeletal frame 15 may also be comprised of a plurality of filaments or fibers which are wound or braided together to form a continuous structure. Finally, in a preferred embodiment, skeletal frame 15 may be formed by removing material from a tubular element using a LASER cutting process.
Often it is beneficial to both stmt and treat a localized area of a diseased vessel. A therapeutic agent, therefore, can be incorporated into a polymer and applied to stmt 10 as a polymeric surface treatment. The incorporation of a therapeutic agent into a surface treatment greatly enhances the scope of this medical device by transforming the stmt into a drug-delivery system. Drugs and treatments which utilize anti-thrombogenic agents, anti-angiogenisis agents, anti-proliferative agents, growth factors, and radiochemicals may be readily deployed from within the matrix of to the polymeric surface treatment. Specific examples of preferred therapeutic agents include angiopeptin, colchicine, lovastatin, trapidil, ticlopidine, hirudin, Taxol, and heparin. Specific examples of growth factors which may serve as therapeutic agents include VEGF, TGF-beta, IGF, PDGF, and FGF.
The application of such a surface treatment is generally accomplished by applying a coating solution to stmt 10. Typically, this coating solution includes a solvent, a polymer dissolved in the solvent, and a therapeutic substance dispersed in the solvent. The coating solution may be applied to stmt 10 using a variety of methods. For example, the solution may be applied to stmt 10 by immersing stmt
10 in the coating solution. Alternately, the coating solution may be applied to stmt 10 2o with a brush. Finally, in a preferred embodiment, the coating solution may be sprayed onto stmt 10. Airbrushes suitable for spraying a solution of this type are commercially available from Badger Air-Brush of Franklin Park Illinois.
Solvent selection is critical to a functioning surface treatment. It is essential that the solvent is capable of placing the polymer into solution, and that the solvent and polymer chosen do not materially alter the therapeutic character of the therapeutic agent. On the other hand, the therapeutic agent needs only to be dispersed throughout the solvent. The therapeutic agent, therefore, may be either in a true solution with the solvent or dispersed in fine particles within the solvent.
Examples of some suitable polymer/solvent/therapeutic agent combinations 3o can include: polylactic acid/trichloroethane/colchicine;
polyurethane/tetrahydrofuron/Taxol; (PLA/PCL)/dimethylformamide/hirudin;
(PLA/PGA)/ethylacetate/ticlopidine; and polyethylene oxide/ethanol/heparin. It should be understood that these combinations are merely exemplary, and it is recognized that other combinations are possible.
Figure 2 shows a magnified, partial plan view of stmt 10, including wires 12 and openings 16. The surfaces of stmt 10 are covered with a polymeric coating 28.
Polymeric coating 28 is created by applying a solution preferably including polymer, solvent, and therapeutic agent to the surfaces of stmt 10 then allowing the solvent to evaporate, thereby leaving on the stmt surface a coating of the polymer and the therapeutic agent. A number of processes may be used to apply the coating solution to stmt 10, including spraying, dipping, brushing, etc.
to It is preferred that polymeric coating 28 be evenly distributed over stmt 10.
Although the procedures for applying the polymeric surface treatments are optimized, they still often leave polymeric fibers, polymeric particles, or other polymeric surface aberrations or imperfections on stmt 10. These aberrations or imperfections in polymeric coating 28 are illustrated in Figure 2. Polymeric imperfections 30 may take on numerous shapes and sizes. Regardless of the application process utilized, several types of imperfections 30 are common. Examples of these imperfections 30 are polymeric fibers 32 which span the openings 16 of the skeletal framework 15, and lumps 34 created by an overabundance of polymeric material in one location.
Imperfections 30 in polymeric coating 28 may be the result of disproportionate 2o application of the coating solution, or the settling of excessive material in a particular location. At a minimum, imperfections 30 are unsightly. More importantly, however, imperfections 30 may create adverse secondary effects.
The adverse secondary effects which may arise are correlated to the type of polymeric imperfections 30. Polymeric fibers 32 are prone to two adverse effects;
fibers 32 may dislodge from stmt 10 or they may release their therapeutic agents into the blood stream. Because polymeric fibers 32 span across openings 16 of stmt 10, they are attached typically at few locations. Expansion of stmt 10 may dislodge these imperfections 32, sending them within the circulatory system. At this point, there exists no control over the drug delivering capabilities of these rogue fibers 32. The 3o release of drugs in undesired locations is likely to cause secondary effects. On the other hand, polymeric fibers 32 may remain attached to stmt 10. Some of the polymeric fibers 32 which remain attached to stmt 10 may not engage the wall of the blood vessel. In this instance, the entire surface area of these polymeric fibers 32 is
Solvent selection is critical to a functioning surface treatment. It is essential that the solvent is capable of placing the polymer into solution, and that the solvent and polymer chosen do not materially alter the therapeutic character of the therapeutic agent. On the other hand, the therapeutic agent needs only to be dispersed throughout the solvent. The therapeutic agent, therefore, may be either in a true solution with the solvent or dispersed in fine particles within the solvent.
Examples of some suitable polymer/solvent/therapeutic agent combinations 3o can include: polylactic acid/trichloroethane/colchicine;
polyurethane/tetrahydrofuron/Taxol; (PLA/PCL)/dimethylformamide/hirudin;
(PLA/PGA)/ethylacetate/ticlopidine; and polyethylene oxide/ethanol/heparin. It should be understood that these combinations are merely exemplary, and it is recognized that other combinations are possible.
Figure 2 shows a magnified, partial plan view of stmt 10, including wires 12 and openings 16. The surfaces of stmt 10 are covered with a polymeric coating 28.
Polymeric coating 28 is created by applying a solution preferably including polymer, solvent, and therapeutic agent to the surfaces of stmt 10 then allowing the solvent to evaporate, thereby leaving on the stmt surface a coating of the polymer and the therapeutic agent. A number of processes may be used to apply the coating solution to stmt 10, including spraying, dipping, brushing, etc.
to It is preferred that polymeric coating 28 be evenly distributed over stmt 10.
Although the procedures for applying the polymeric surface treatments are optimized, they still often leave polymeric fibers, polymeric particles, or other polymeric surface aberrations or imperfections on stmt 10. These aberrations or imperfections in polymeric coating 28 are illustrated in Figure 2. Polymeric imperfections 30 may take on numerous shapes and sizes. Regardless of the application process utilized, several types of imperfections 30 are common. Examples of these imperfections 30 are polymeric fibers 32 which span the openings 16 of the skeletal framework 15, and lumps 34 created by an overabundance of polymeric material in one location.
Imperfections 30 in polymeric coating 28 may be the result of disproportionate 2o application of the coating solution, or the settling of excessive material in a particular location. At a minimum, imperfections 30 are unsightly. More importantly, however, imperfections 30 may create adverse secondary effects.
The adverse secondary effects which may arise are correlated to the type of polymeric imperfections 30. Polymeric fibers 32 are prone to two adverse effects;
fibers 32 may dislodge from stmt 10 or they may release their therapeutic agents into the blood stream. Because polymeric fibers 32 span across openings 16 of stmt 10, they are attached typically at few locations. Expansion of stmt 10 may dislodge these imperfections 32, sending them within the circulatory system. At this point, there exists no control over the drug delivering capabilities of these rogue fibers 32. The 3o release of drugs in undesired locations is likely to cause secondary effects. On the other hand, polymeric fibers 32 may remain attached to stmt 10. Some of the polymeric fibers 32 which remain attached to stmt 10 may not engage the wall of the blood vessel. In this instance, the entire surface area of these polymeric fibers 32 is
11 free to release therapeutic agent directly into the blood stream, causing other secondary effects.
Polymeric lumps 34 caused by an overabundance of polymeric material in a localized area may also cause secondary effects. As mentioned above, the goal of applying a polymeric surface treatment upon a stmt 10 is to have uniform coverage and uniform release of a therapeutic substance. When there are areas of excess coverage on stmt 10, the targeted diseased tissue may receive a non-uniform dosage of the released therapeutic agent. For therapeutic agents, especially ones which promote or restrict endothelial cell growth, uneven release may cause non-optimal l0 treatment. Another problem created by lumps 34 is that the lumps 34 may be in a location on stmt 10 where they do not contact the wall of the blood vessel. In this instance, the entire surface area of the lumps 34 will be free to release therapeutic agent directly into the blood stream, causing other secondary effects.
Figure 3 is a plan view of a stmt 10 and a tool 300. As described previously, stmt 10 includes wires 12, openings 16, and a lumen 20. A stream 302 of a gas 304 is shown exiting tool 300. In a preferred embodiment, tool 300 includes a generally tubular member 306 having a lumen extending therethough which is open at a distal end 322. The outer diameter of tubular member 306 is selected so that distal end 322 of tool 300 may readily enter lumen 20 of stmt 10. A number of materials may be used to fabricate tool 300 including metallic and non-metallic materials. In a preferred embodiment, tool 300 is fabricated from hypodermic tubing.
Hypodermic tubing is preferred because it is readily available with an appropriate outer diameter.
Tool 300 is in fluid communication with a supply (not shown) of compressed gas 304. Compressed gas 304 is preferably compressed air because it is inexpensive and readily available. Other gasses 304 may be used without departing from the spirit and scope of this invention. For example, acceptable results may be obtained using helium, nitrogen, argon, and carbon dioxide. Other gases may also be suitable for this application, including gasses which are not normally present in air.
Compressed gas 304 is released to atmosphere through tool 300 to create stream 302.
Tool 300 may be moved as indicated by a direction vector 310 in Figure 3.
When tool 300 is moved in the direction indicated by vector 310, tool 300 is made to enter lumen 20 of stmt 10. Tool 300 may also be rotated as illustrated by direction vector 312, to change the angle at which stream 302 strikes the surfaces of stmt 10.
Polymeric lumps 34 caused by an overabundance of polymeric material in a localized area may also cause secondary effects. As mentioned above, the goal of applying a polymeric surface treatment upon a stmt 10 is to have uniform coverage and uniform release of a therapeutic substance. When there are areas of excess coverage on stmt 10, the targeted diseased tissue may receive a non-uniform dosage of the released therapeutic agent. For therapeutic agents, especially ones which promote or restrict endothelial cell growth, uneven release may cause non-optimal l0 treatment. Another problem created by lumps 34 is that the lumps 34 may be in a location on stmt 10 where they do not contact the wall of the blood vessel. In this instance, the entire surface area of the lumps 34 will be free to release therapeutic agent directly into the blood stream, causing other secondary effects.
Figure 3 is a plan view of a stmt 10 and a tool 300. As described previously, stmt 10 includes wires 12, openings 16, and a lumen 20. A stream 302 of a gas 304 is shown exiting tool 300. In a preferred embodiment, tool 300 includes a generally tubular member 306 having a lumen extending therethough which is open at a distal end 322. The outer diameter of tubular member 306 is selected so that distal end 322 of tool 300 may readily enter lumen 20 of stmt 10. A number of materials may be used to fabricate tool 300 including metallic and non-metallic materials. In a preferred embodiment, tool 300 is fabricated from hypodermic tubing.
Hypodermic tubing is preferred because it is readily available with an appropriate outer diameter.
Tool 300 is in fluid communication with a supply (not shown) of compressed gas 304. Compressed gas 304 is preferably compressed air because it is inexpensive and readily available. Other gasses 304 may be used without departing from the spirit and scope of this invention. For example, acceptable results may be obtained using helium, nitrogen, argon, and carbon dioxide. Other gases may also be suitable for this application, including gasses which are not normally present in air.
Compressed gas 304 is released to atmosphere through tool 300 to create stream 302.
Tool 300 may be moved as indicated by a direction vector 310 in Figure 3.
When tool 300 is moved in the direction indicated by vector 310, tool 300 is made to enter lumen 20 of stmt 10. Tool 300 may also be rotated as illustrated by direction vector 312, to change the angle at which stream 302 strikes the surfaces of stmt 10.
12 Tool 300 of Figure 3 may be used in conjunction with a method of applying a polymer coating 28 to stmt 10. The process begins with the step of preparing a coating solution preferably including a polymer, a solvent, and a therapeutic substance. The coating solution is then applied to the stmt by dipping, spraying, or any other acceptable method. Tool 300 is then used to direct gas stream 302 so that it impinges on the surfaces of stmt 10. When gas 304 of gas stream 302 strikes the surfaces of stmt 10 it displaces excess coating solution.
Tool 300 may be moved to direct gas stream 302 at stmt 10 from a plurality of different locations and from a plurality of different angles. For example, tool 300 may be moved as shown by vector 310 so that tool 300 passes partially or completely through lumen 20 of stmt 10. Tool 300 may also be rotated as shown by vector so that gas stream 302 strikes stmt 10 at a plurality of angles. The position of tool 300 relative to stmt 10 may also be changed without deviating from the spirit and scope of the invention.
The flow of gas 304 through openings 16 and around wires 12 is sufficient to displace excess coating solution. Any lumps, fibers, etc. formed by the coating solution will be blown off the surfaces of stmt 10 or distributed more evenly over such surfaces by gas stream 302. Once the excess coating solution has been removed from or redistributed on the surfaces of stmt 10, the remaining solution on the stmt 2o which is still liquid generally distributes evenly across the surface of the stmt 10. The solvent in the coating solution is then allowed to evaporate thereby leaving on the surfaces of stmt 10 a polymer coating 28. As described above, polymer coating ideally includes a therapeutic agent. Because all imperfections were removed before the coating solution was allowed to dry, the polymer coating 28 resulting from this process is evenly distributed across the surfaces of stmt 10.
Figure 4 shows a magnified, partial plan view of stmt 10, including wires 12 and openings 16. A polymeric coating 28 has been applied to stmt 10 of Figure using the method described above. A coating solution including polymer, solvent, and therapeutic agent is applied to stmt 10, excess coating was removed from stmt 10, and the remaining solution on the stmt which is still generally liquid, distributes evenly across the surface of the stmt. The solvent was allowed to evaporate, thereby leaving on the stmt surface a coating of the polymer and the therapeutic agent. As seen in Figure 4, the resulting polymer coating is evenly distributed across the
Tool 300 may be moved to direct gas stream 302 at stmt 10 from a plurality of different locations and from a plurality of different angles. For example, tool 300 may be moved as shown by vector 310 so that tool 300 passes partially or completely through lumen 20 of stmt 10. Tool 300 may also be rotated as shown by vector so that gas stream 302 strikes stmt 10 at a plurality of angles. The position of tool 300 relative to stmt 10 may also be changed without deviating from the spirit and scope of the invention.
The flow of gas 304 through openings 16 and around wires 12 is sufficient to displace excess coating solution. Any lumps, fibers, etc. formed by the coating solution will be blown off the surfaces of stmt 10 or distributed more evenly over such surfaces by gas stream 302. Once the excess coating solution has been removed from or redistributed on the surfaces of stmt 10, the remaining solution on the stmt 2o which is still liquid generally distributes evenly across the surface of the stmt 10. The solvent in the coating solution is then allowed to evaporate thereby leaving on the surfaces of stmt 10 a polymer coating 28. As described above, polymer coating ideally includes a therapeutic agent. Because all imperfections were removed before the coating solution was allowed to dry, the polymer coating 28 resulting from this process is evenly distributed across the surfaces of stmt 10.
Figure 4 shows a magnified, partial plan view of stmt 10, including wires 12 and openings 16. A polymeric coating 28 has been applied to stmt 10 of Figure using the method described above. A coating solution including polymer, solvent, and therapeutic agent is applied to stmt 10, excess coating was removed from stmt 10, and the remaining solution on the stmt which is still generally liquid, distributes evenly across the surface of the stmt. The solvent was allowed to evaporate, thereby leaving on the stmt surface a coating of the polymer and the therapeutic agent. As seen in Figure 4, the resulting polymer coating is evenly distributed across the
13 surfaces of stmt 10. As described previously, polymeric coating 28 includes a polymer and a therapeutic agent, in a preferred embodiment. In an alternate embodiment, polymeric coating 28 may be comprised of a polymer.
Figure 5 is a plan view of a stmt 10 and an alternate tool 500. As described previously, stmt 10 includes wires 12, openings 16, and a lumen 20. A
plurality of gas streams 502 are shown exiting tool 500. In a preferred embodiment, tool includes a tubular member 506 and an end cap 508. Tubular member 506 includes a lumen 520 and a plurality of apertures 530. Apertures 530 provide a fluid passage from lumen 520 of tubular member 506 to the atmosphere surrounding tubular member 506. Although apertures 530 are illustrated as slots in Figure 5, it should be understood that other embodiments of apertures 530 are possible without deviating from the spirit and scope of the invention. For example, apertures 530 may be round holes.
Tool 500 is in fluid communication with a supply (not shown) of compressed gas 504. The compressed gas 504 is released to atmosphere through tool 500 to create streams 502. Tool 500 may be moved as indicated by a direction vector 510 in Figure 5. In this manner, tool 500 may be moved through lumen 520 of stmt 10, so that streams 502 may be passed along the entire length of stmt 10. Tool 500 may also be rotated as illustrated by direction vector 512. Rotating tool 500 allows streams 502 to 2o pass across the entire circumference of stmt 10.
Tool 500 of Figure 5 may be used in conjunction with a method of applying a polymer coating 28 to stmt 10. The process begins with the step of preparing a coating solution preferably including a polymer, a solvent, and a therapeutic substance. The coating solution is then applied to the stmt by dipping, spraying, or any other acceptable method. Tool 500 is then used to direct gas streams 502 so that they impinge on the surfaces of stmt 10. When gas 504 of gas streams 502 strikes the surfaces of stmt 10 it displaces excess coating solution.
During this process, tool 500 may be rotated and moved in a linear direction.
For example, tool 500 may be in continuous rotary motion as indicated by vector 512, such that streams 502 generally impinge on the entire circumference of stmt 10. By way of a second example, tool 500 may be moved in a linear direction, so that streams 502 pass across the entire length of stmt 10. It should be understood that tool 500
Figure 5 is a plan view of a stmt 10 and an alternate tool 500. As described previously, stmt 10 includes wires 12, openings 16, and a lumen 20. A
plurality of gas streams 502 are shown exiting tool 500. In a preferred embodiment, tool includes a tubular member 506 and an end cap 508. Tubular member 506 includes a lumen 520 and a plurality of apertures 530. Apertures 530 provide a fluid passage from lumen 520 of tubular member 506 to the atmosphere surrounding tubular member 506. Although apertures 530 are illustrated as slots in Figure 5, it should be understood that other embodiments of apertures 530 are possible without deviating from the spirit and scope of the invention. For example, apertures 530 may be round holes.
Tool 500 is in fluid communication with a supply (not shown) of compressed gas 504. The compressed gas 504 is released to atmosphere through tool 500 to create streams 502. Tool 500 may be moved as indicated by a direction vector 510 in Figure 5. In this manner, tool 500 may be moved through lumen 520 of stmt 10, so that streams 502 may be passed along the entire length of stmt 10. Tool 500 may also be rotated as illustrated by direction vector 512. Rotating tool 500 allows streams 502 to 2o pass across the entire circumference of stmt 10.
Tool 500 of Figure 5 may be used in conjunction with a method of applying a polymer coating 28 to stmt 10. The process begins with the step of preparing a coating solution preferably including a polymer, a solvent, and a therapeutic substance. The coating solution is then applied to the stmt by dipping, spraying, or any other acceptable method. Tool 500 is then used to direct gas streams 502 so that they impinge on the surfaces of stmt 10. When gas 504 of gas streams 502 strikes the surfaces of stmt 10 it displaces excess coating solution.
During this process, tool 500 may be rotated and moved in a linear direction.
For example, tool 500 may be in continuous rotary motion as indicated by vector 512, such that streams 502 generally impinge on the entire circumference of stmt 10. By way of a second example, tool 500 may be moved in a linear direction, so that streams 502 pass across the entire length of stmt 10. It should be understood that tool 500
14 may be moved in a manner different than that shown in the above examples without deviating from the spirit and scope of the invention.
The flow of gas 504 through openings 16 and around wires 12 is sufficient to displace excess coating solution (e.g. any lumps, fibers, etc. formed by the coating solution will be blown off the surfaces of stmt 10 by gas streams 502). Once the excess coating solution has been removed from or redistributed on the surfaces of stmt 10, the remaining liquid solution generally distributes evenly over the stmt surface 10. The solvent in the coating solution is allowed to evaporate thereby leaving on the surfaces of stmt 10 a polymer coating 28, which preferably includes a therapeutic agent. Because all imperfections were removed before the coating solution was allowed to dry, the polymer coating 28 resulting from this process is evenly distributed across the surfaces of stmt 10.
Figure 6 is a plan view of a stmt 10 and a tool 600. As described previously, stmt 10 includes wires 12, openings 16, and a lumen 20. A plurality of gas streams 602 are shown exiting tool 600. In a preferred embodiment, tool 600 includes a tubular member 606 and an end cap 608. Tubular member 606 includes a lumen 620 and a plurality of apertures 630. Apertures 630 provide a fluid passage from lumen 620 of tubular member 606 to the atmosphere surrounding tubular member 606. In the embodiment of figure 6, apertures 630 are slots which are generally perpendicular 2o to the axis of tubular member 606. As seen in figure 6, apertures 630 extend beyond the center of tubular member 606.
Lumen 620 of tool 600 is in fluid communication with a supply (not shown) of compressed gas 604. Compressed gas 604 is released to atmosphere through apertures 630 in tool 600 to create streams 602. As described above, the embodiment of figure 6 includes apertures 630 which are slots extending beyond the center of tubular member 606. As seen in figure 6, apertures 630 are adapted so that streams 602 of gas 604 may exit tool 600 along its entire circumference. This arrangement of apertures 630 creates a 360° pattern of streams 602 around tool 600.
Tool 600 may be moved as indicated by a direction vector 610 in Figure 6.
3o When tool 600 is moved in the direction indicated by vector 610, tool 600 is made to travel through lumen 20 of stmt 10.
Tool 600 of Figure 6 may be used in conjunction with a method of applying a polymer coating 28 to stmt 10. The process begins with the step of preparing a coating solution preferably including a polymer, a solvent, and a therapeutic substance. The coating solution is then applied to the stmt by dipping, spraying, or any other acceptable method. Tool 600 is then used to direct gas streams 602 so that they impinge on the surfaces of stmt 10. When gas 604 of gas streams 602 strikes the surfaces of stmt 10 it displaces excess coating solution. Tool 600 may be moved during this process to assure that gas streams 602 impinge upon substantially all the surfaces of stmt 10.
The flow of gas 604 through openings 16 and around wires 12 is sufficient to displace excess coating solution (e.g. any lumps, fibers, etc. formed by the coating to solution will be blown off the surfaces of stmt 10 by gas streams 602).
Once the excess coating solution has been removed from the surfaces of stmt 10, the remaining liquid solution on the stmt distributes evenly across the surface of the stmt 10. The solvent in the coating solution is allowed to evaporate thereby leaving on the surfaces of stmt 10 a polymer coating 28, which preferably includes a therapeutic agent.
Because all imperfections were removed before the coating solution was allowed to dry, the polymer coating 28 resulting from this process is evenly distributed across the surfaces of stmt 10.
Figure 7 is a plan view of a stmt 10, a tool 700, and a mandrel 730. As described previously, stmt 10 includes wires 12, openings 16, and a lumen 20.
Tool 700 is similar to the tool of figure 3 being a generally tubular member having a lumen therethrough which is open at one end. A stream 702 of a gas 704 is shown exiting tool 700. In a preferred embodiment, tool 700 includes a tubular member 706 having a lumen 720 and a distal end 708. Mandrel 730 is positioned so that its distal end 732 is proximate distal end 708 of tubular member 706 creating a narrow fluid passage 734. The aperture size of tool 700 may be varied by altering the position of the mandrel 730 relative to the distal end of tubular member 706. This will control the size and force of the gas stream impinging on the stmt 10 with the gas jet being uniform over the entire circumference of the stmt.
Tool 700 is in fluid communication with a supply (not shown) of compressed 3o gas 704. The compressed gas 704 is released to atmosphere through tubular member 706 and narrow fluid passage 734. When gas 704 exits narrow fluid passage 734 it is traveling in a direction which will cause it to impinge on the surfaces of stmt 10.
Tool 700 and mandrel 730 may be moved as indicated by a direction vector 710 in Figure 7. When tool 700 and mandrel 730 are moved in the direction indicated by vector 710, tool 700 and mandrel 730 may be made to pass through lumen 20 of stmt 10.
Tool 700 and mandrel 730 of Figure 7 may be used in conjunction with a method of applying a polymer coating 28 to stmt 10. The process begins with the step of preparing a coating solution preferably including a polymer, a solvent, and a therapeutic substance. The coating solution is then applied to the stmt by dipping, spraying, or any other acceptable method. Tool 700 and mandrel 730 are then used to direct gas stream 702 so that it impinges on the surfaces of stmt 10. When gas 704 of gas stream 702 strikes the surfaces of stmt 10 excess coating solution is displaced.
Tool 700 and mandrel 730 may be moved during this process to assure that gas stream 702 impinges upon substantially all the surfaces of stmt 10.
The flow of gas 704 through openings 16 and around wires 12 is sufficient to displace excess coating solution (e.g. any lumps, fibers, etc. formed by the coating solution will be blown off the surfaces of stmt 10 by gas stream 702). Once the excess coating solution has been removed from or redistributed on the surfaces of stmt 10, remaining liquid solution generally distributes evenly across the surface of the stmt 10. The solvent in the coating solution is allowed to evaporate thereby leaving on the surfaces of stmt 10 a polymer coating 28, which preferably includes a therapeutic agent. Because all imperfections were removed before the coating solution was allowed to dry, the polymer coating 28 resulting from this process is evenly distributed across the surfaces of stmt 10.
It should be understood that the coating method described above may be used in conjunction with any stmt design. For example, this coating method may be used with both self expanding and balloon expandable stems. The coating method described above may also be used with implantable medical devices other than stems.
For example, a thrombosis filter may be coated using the coating method described above.
3o Figure 8 is a perspective view of a thrombosis filter 820. Thrombosis filter 820 includes a body member 822 and a plurality of elongated struts 824. Struts each having a joined end 826 and a free end 828. Joined end 826 of each strut 824 is fixedly attached to body member 822.
Struts 824 may be comprised of any biocompatible material possessing the structural and mechanical attributes necessary to retain thrombus filter 820 in a blood vessel and capture thrombi. The material of struts 824 may be a single material or a combination of materials. The material of struts 824 may be metallic or non-metallic.
Stainless steel, titanium, tantalum, and nickel-titanium alloys have all been found to be acceptable metallic materials for struts 824. Preferred non-metallic materials may be selected from the following list, which is not exhaustive: poly(L-lactide) (PLLA), poly(D,L-lactide) (PLA), polyglycolide (PGA), poly(L-lactide-co-D,L-lactide) (PLLA/PLA), poly(L-lactide-co-glycolide) (PLLA/PGA), poly(D, L-lactide-co-1 o glycolide) (PLA/PGA), poly(glycolide-co-trimethylene carbonate) (PGA/PTMC), polyethylene oxide (PEO), polydioxanone (PDS), polycaprolactone (PCL), polyhydroxylbutyrate (PHBT), poly(phosphazene), polyp,L-lactide-co-caprolactone) (PLA/PCL), poly(glycolide-co-caprolactone) (PGA/PCL), polyanhydrides (PAN), poly(ortho esters), poly(phoshate ester), poly(amino acid), poly(hydroxy butyrate), polyacrylate, polyacrylamid, poly(hydroxyethyl methacrylate), polyurethane, polysiloxane and their copolymers.
Struts 824 radiate outwardly from body member 822 such that thrombosis filter 820 is generally conical in shape. When thrombosis filter 820 is deployed inside a blood vessel, free ends 828 engage the blood vessel wall. Body member 822 is held 2o in a position proximate the center of the blood vessel by the plurality of struts 824 which engage the blood vessel walls with opposing force vectors.
The walls of the blood vessel are lined with a thin inner membrane, referred to as an intima or as a thelium. When thrombus filter 820 is implanted in a blood vessel, the thelium is disrupted by free ends 828 of struts 824. When free ends 828 of struts 824 disrupt this inner membrane, the body responds with a process which may be referred to as neointimal hyperplasia, or endothelial growth. As a result of this process, the disrupted area of the thelium is overgrown with a number of new cells.
In a short time, free ends 828 of struts 824 become encapsulated with new cell growth. Due to this endothelial growth, thrombosis filters placed in the blood vessel of a patient become affixed in the blood vessel walls within two weeks after being implanted. Because free ends 828 of struts 824 become fixed to the blood vessel walls in this way, removal of thrombus filter 820 using minimally invasive methods will be difficult if not impossible after it has been in place for more than two weeks.
Applying a coating including a therapeutic substance in a polymeric carrier to thrombosis filter 820 may prevent endothelial growth from encapsulating free ends 828 of struts 824. If encapsulation of free ends 828 of struts 824 is partially or completely prevented, the ability to remove percutaneously remove thrombus filter 820 will be greatly enhanced. The coating including the therapeutic substance may be applied selectively to free ends 828 of struts 824. Alternately, the coating may be applied to substantially all the surfaces of thrombosis filter 820.
When thrombosis filter 820 is disposed in a blood vessel, the conical formation of struts 824 acts to trap, or capture blood clots. The generally conical 1o shape of the formation of struts 824 serves to urge captured blood clots toward the center of the blood flow. The flow of blood around the captured blood clots allows the body's natural lysing process to dissolve the clots. Applying a coating including a therapeutic substance in a polymeric carrier to the vascular filter may assist the body in dissolving blood clots.
A tool 900 which may be used in conjunction with a method of coating thrombosis filter 820 is also shown in Figure 8. A plurality of gas streams 902 are shown exiting tool 900. In a preferred embodiment, tool 900 is a generally tubular member including a lumen 910 and a plurality of apertures 912. Apertures 912 provide a fluid passage from lumen 910 of tool 900 to the atmosphere surrounding tool 900. Although apertures 912 are illustrated as round holes in Figure 8, it should be understood that other embodiments of apertures 912 are possible without deviating from the spirit and scope of the invention. For example, apertures 912 may be slots.
Lumen 910 of tool 900 is in fluid communication with a supply (not shown) of compressed gas 904. Compressed gas 904 is released to atmosphere through tool to create streams 902.
As was previously mentioned, tool 900 of Figure 8 may be used in conjunction with a method of applying a polymer coating to thrombosis filter 820. The process begins with the step of preparing a coating solution preferably including a polymer, a solvent, and a therapeutic substance. The coating solution is then applied to 3o thrombosis filter 820 by dipping, spraying, or any other acceptable method.
Tool 900 is then used to direct gas streams 902 so that they impinge on the surfaces of thrombosis filter 820. When gas 904 of gas streams 902 strikes the surfaces of thrombosis filter 820, it displaces excess coating solution.
To assure that gas streams 902 impinge upon substantially all the surfaces of thrombosis filter 820, tool 900 may be rotated and moved in a linear direction. Tool 900 may also be moved to a position other than the position shown in Figure 8 without deviating from the spirit or scope of this invention.
The flow of gas 904 around struts 824 and body member 822 is sufficient to displace excess coating solution. Once the excess coating solution has been removed from or redistributed on the surfaces of thrombosis filter 820, the solvent in the coating solution is allowed to evaporate thereby leaving on the surface of thrombosis filter 820 a polymer coating, which preferably includes a therapeutic agent.
Because 1o all imperfections were removed before the coating solution was allowed to dry, the polymer coating resulting from this process is evenly distributed across the surfaces of thrombosis filter 820.
Numerous advantages of the invention covered by this document have been set forth in the foregoing description. It will be understood, however, that this disclosure is, in many respects, only illustrative. Changes may be made in details, particularly in matters of shape, size, and arrangement of parts without exceeding the scope of the invention. The invention's scope is, of course, defined in the language in which the appended claims are expressed.
The flow of gas 504 through openings 16 and around wires 12 is sufficient to displace excess coating solution (e.g. any lumps, fibers, etc. formed by the coating solution will be blown off the surfaces of stmt 10 by gas streams 502). Once the excess coating solution has been removed from or redistributed on the surfaces of stmt 10, the remaining liquid solution generally distributes evenly over the stmt surface 10. The solvent in the coating solution is allowed to evaporate thereby leaving on the surfaces of stmt 10 a polymer coating 28, which preferably includes a therapeutic agent. Because all imperfections were removed before the coating solution was allowed to dry, the polymer coating 28 resulting from this process is evenly distributed across the surfaces of stmt 10.
Figure 6 is a plan view of a stmt 10 and a tool 600. As described previously, stmt 10 includes wires 12, openings 16, and a lumen 20. A plurality of gas streams 602 are shown exiting tool 600. In a preferred embodiment, tool 600 includes a tubular member 606 and an end cap 608. Tubular member 606 includes a lumen 620 and a plurality of apertures 630. Apertures 630 provide a fluid passage from lumen 620 of tubular member 606 to the atmosphere surrounding tubular member 606. In the embodiment of figure 6, apertures 630 are slots which are generally perpendicular 2o to the axis of tubular member 606. As seen in figure 6, apertures 630 extend beyond the center of tubular member 606.
Lumen 620 of tool 600 is in fluid communication with a supply (not shown) of compressed gas 604. Compressed gas 604 is released to atmosphere through apertures 630 in tool 600 to create streams 602. As described above, the embodiment of figure 6 includes apertures 630 which are slots extending beyond the center of tubular member 606. As seen in figure 6, apertures 630 are adapted so that streams 602 of gas 604 may exit tool 600 along its entire circumference. This arrangement of apertures 630 creates a 360° pattern of streams 602 around tool 600.
Tool 600 may be moved as indicated by a direction vector 610 in Figure 6.
3o When tool 600 is moved in the direction indicated by vector 610, tool 600 is made to travel through lumen 20 of stmt 10.
Tool 600 of Figure 6 may be used in conjunction with a method of applying a polymer coating 28 to stmt 10. The process begins with the step of preparing a coating solution preferably including a polymer, a solvent, and a therapeutic substance. The coating solution is then applied to the stmt by dipping, spraying, or any other acceptable method. Tool 600 is then used to direct gas streams 602 so that they impinge on the surfaces of stmt 10. When gas 604 of gas streams 602 strikes the surfaces of stmt 10 it displaces excess coating solution. Tool 600 may be moved during this process to assure that gas streams 602 impinge upon substantially all the surfaces of stmt 10.
The flow of gas 604 through openings 16 and around wires 12 is sufficient to displace excess coating solution (e.g. any lumps, fibers, etc. formed by the coating to solution will be blown off the surfaces of stmt 10 by gas streams 602).
Once the excess coating solution has been removed from the surfaces of stmt 10, the remaining liquid solution on the stmt distributes evenly across the surface of the stmt 10. The solvent in the coating solution is allowed to evaporate thereby leaving on the surfaces of stmt 10 a polymer coating 28, which preferably includes a therapeutic agent.
Because all imperfections were removed before the coating solution was allowed to dry, the polymer coating 28 resulting from this process is evenly distributed across the surfaces of stmt 10.
Figure 7 is a plan view of a stmt 10, a tool 700, and a mandrel 730. As described previously, stmt 10 includes wires 12, openings 16, and a lumen 20.
Tool 700 is similar to the tool of figure 3 being a generally tubular member having a lumen therethrough which is open at one end. A stream 702 of a gas 704 is shown exiting tool 700. In a preferred embodiment, tool 700 includes a tubular member 706 having a lumen 720 and a distal end 708. Mandrel 730 is positioned so that its distal end 732 is proximate distal end 708 of tubular member 706 creating a narrow fluid passage 734. The aperture size of tool 700 may be varied by altering the position of the mandrel 730 relative to the distal end of tubular member 706. This will control the size and force of the gas stream impinging on the stmt 10 with the gas jet being uniform over the entire circumference of the stmt.
Tool 700 is in fluid communication with a supply (not shown) of compressed 3o gas 704. The compressed gas 704 is released to atmosphere through tubular member 706 and narrow fluid passage 734. When gas 704 exits narrow fluid passage 734 it is traveling in a direction which will cause it to impinge on the surfaces of stmt 10.
Tool 700 and mandrel 730 may be moved as indicated by a direction vector 710 in Figure 7. When tool 700 and mandrel 730 are moved in the direction indicated by vector 710, tool 700 and mandrel 730 may be made to pass through lumen 20 of stmt 10.
Tool 700 and mandrel 730 of Figure 7 may be used in conjunction with a method of applying a polymer coating 28 to stmt 10. The process begins with the step of preparing a coating solution preferably including a polymer, a solvent, and a therapeutic substance. The coating solution is then applied to the stmt by dipping, spraying, or any other acceptable method. Tool 700 and mandrel 730 are then used to direct gas stream 702 so that it impinges on the surfaces of stmt 10. When gas 704 of gas stream 702 strikes the surfaces of stmt 10 excess coating solution is displaced.
Tool 700 and mandrel 730 may be moved during this process to assure that gas stream 702 impinges upon substantially all the surfaces of stmt 10.
The flow of gas 704 through openings 16 and around wires 12 is sufficient to displace excess coating solution (e.g. any lumps, fibers, etc. formed by the coating solution will be blown off the surfaces of stmt 10 by gas stream 702). Once the excess coating solution has been removed from or redistributed on the surfaces of stmt 10, remaining liquid solution generally distributes evenly across the surface of the stmt 10. The solvent in the coating solution is allowed to evaporate thereby leaving on the surfaces of stmt 10 a polymer coating 28, which preferably includes a therapeutic agent. Because all imperfections were removed before the coating solution was allowed to dry, the polymer coating 28 resulting from this process is evenly distributed across the surfaces of stmt 10.
It should be understood that the coating method described above may be used in conjunction with any stmt design. For example, this coating method may be used with both self expanding and balloon expandable stems. The coating method described above may also be used with implantable medical devices other than stems.
For example, a thrombosis filter may be coated using the coating method described above.
3o Figure 8 is a perspective view of a thrombosis filter 820. Thrombosis filter 820 includes a body member 822 and a plurality of elongated struts 824. Struts each having a joined end 826 and a free end 828. Joined end 826 of each strut 824 is fixedly attached to body member 822.
Struts 824 may be comprised of any biocompatible material possessing the structural and mechanical attributes necessary to retain thrombus filter 820 in a blood vessel and capture thrombi. The material of struts 824 may be a single material or a combination of materials. The material of struts 824 may be metallic or non-metallic.
Stainless steel, titanium, tantalum, and nickel-titanium alloys have all been found to be acceptable metallic materials for struts 824. Preferred non-metallic materials may be selected from the following list, which is not exhaustive: poly(L-lactide) (PLLA), poly(D,L-lactide) (PLA), polyglycolide (PGA), poly(L-lactide-co-D,L-lactide) (PLLA/PLA), poly(L-lactide-co-glycolide) (PLLA/PGA), poly(D, L-lactide-co-1 o glycolide) (PLA/PGA), poly(glycolide-co-trimethylene carbonate) (PGA/PTMC), polyethylene oxide (PEO), polydioxanone (PDS), polycaprolactone (PCL), polyhydroxylbutyrate (PHBT), poly(phosphazene), polyp,L-lactide-co-caprolactone) (PLA/PCL), poly(glycolide-co-caprolactone) (PGA/PCL), polyanhydrides (PAN), poly(ortho esters), poly(phoshate ester), poly(amino acid), poly(hydroxy butyrate), polyacrylate, polyacrylamid, poly(hydroxyethyl methacrylate), polyurethane, polysiloxane and their copolymers.
Struts 824 radiate outwardly from body member 822 such that thrombosis filter 820 is generally conical in shape. When thrombosis filter 820 is deployed inside a blood vessel, free ends 828 engage the blood vessel wall. Body member 822 is held 2o in a position proximate the center of the blood vessel by the plurality of struts 824 which engage the blood vessel walls with opposing force vectors.
The walls of the blood vessel are lined with a thin inner membrane, referred to as an intima or as a thelium. When thrombus filter 820 is implanted in a blood vessel, the thelium is disrupted by free ends 828 of struts 824. When free ends 828 of struts 824 disrupt this inner membrane, the body responds with a process which may be referred to as neointimal hyperplasia, or endothelial growth. As a result of this process, the disrupted area of the thelium is overgrown with a number of new cells.
In a short time, free ends 828 of struts 824 become encapsulated with new cell growth. Due to this endothelial growth, thrombosis filters placed in the blood vessel of a patient become affixed in the blood vessel walls within two weeks after being implanted. Because free ends 828 of struts 824 become fixed to the blood vessel walls in this way, removal of thrombus filter 820 using minimally invasive methods will be difficult if not impossible after it has been in place for more than two weeks.
Applying a coating including a therapeutic substance in a polymeric carrier to thrombosis filter 820 may prevent endothelial growth from encapsulating free ends 828 of struts 824. If encapsulation of free ends 828 of struts 824 is partially or completely prevented, the ability to remove percutaneously remove thrombus filter 820 will be greatly enhanced. The coating including the therapeutic substance may be applied selectively to free ends 828 of struts 824. Alternately, the coating may be applied to substantially all the surfaces of thrombosis filter 820.
When thrombosis filter 820 is disposed in a blood vessel, the conical formation of struts 824 acts to trap, or capture blood clots. The generally conical 1o shape of the formation of struts 824 serves to urge captured blood clots toward the center of the blood flow. The flow of blood around the captured blood clots allows the body's natural lysing process to dissolve the clots. Applying a coating including a therapeutic substance in a polymeric carrier to the vascular filter may assist the body in dissolving blood clots.
A tool 900 which may be used in conjunction with a method of coating thrombosis filter 820 is also shown in Figure 8. A plurality of gas streams 902 are shown exiting tool 900. In a preferred embodiment, tool 900 is a generally tubular member including a lumen 910 and a plurality of apertures 912. Apertures 912 provide a fluid passage from lumen 910 of tool 900 to the atmosphere surrounding tool 900. Although apertures 912 are illustrated as round holes in Figure 8, it should be understood that other embodiments of apertures 912 are possible without deviating from the spirit and scope of the invention. For example, apertures 912 may be slots.
Lumen 910 of tool 900 is in fluid communication with a supply (not shown) of compressed gas 904. Compressed gas 904 is released to atmosphere through tool to create streams 902.
As was previously mentioned, tool 900 of Figure 8 may be used in conjunction with a method of applying a polymer coating to thrombosis filter 820. The process begins with the step of preparing a coating solution preferably including a polymer, a solvent, and a therapeutic substance. The coating solution is then applied to 3o thrombosis filter 820 by dipping, spraying, or any other acceptable method.
Tool 900 is then used to direct gas streams 902 so that they impinge on the surfaces of thrombosis filter 820. When gas 904 of gas streams 902 strikes the surfaces of thrombosis filter 820, it displaces excess coating solution.
To assure that gas streams 902 impinge upon substantially all the surfaces of thrombosis filter 820, tool 900 may be rotated and moved in a linear direction. Tool 900 may also be moved to a position other than the position shown in Figure 8 without deviating from the spirit or scope of this invention.
The flow of gas 904 around struts 824 and body member 822 is sufficient to displace excess coating solution. Once the excess coating solution has been removed from or redistributed on the surfaces of thrombosis filter 820, the solvent in the coating solution is allowed to evaporate thereby leaving on the surface of thrombosis filter 820 a polymer coating, which preferably includes a therapeutic agent.
Because 1o all imperfections were removed before the coating solution was allowed to dry, the polymer coating resulting from this process is evenly distributed across the surfaces of thrombosis filter 820.
Numerous advantages of the invention covered by this document have been set forth in the foregoing description. It will be understood, however, that this disclosure is, in many respects, only illustrative. Changes may be made in details, particularly in matters of shape, size, and arrangement of parts without exceeding the scope of the invention. The invention's scope is, of course, defined in the language in which the appended claims are expressed.
Claims (20)
1. A method for applying a polymeric coating to a medical device, the method comprising the steps of:
providing a medical device having a surface thereon;
applying a polymeric material to the surface of the medical device; and directing a stream of gas to impinge on the surface of the medical device, wherein excess liquid polymeric material is removed from or redistributed on the surface of the medical device.
providing a medical device having a surface thereon;
applying a polymeric material to the surface of the medical device; and directing a stream of gas to impinge on the surface of the medical device, wherein excess liquid polymeric material is removed from or redistributed on the surface of the medical device.
2. The method of claim 1, wherein the stream of gas is directed by a generally tubular member defining a lumen and at least one aperture in fluid communication with the lumen.
3. The method of claim 2, wherein the at least one aperture is a hole.
4. The method of claim 2, wherein the at least one aperture is a slot.
5. The method of claim 1, wherein the polymeric material includes a solvent carrier.
6. The method of claim 5, further including the step of evaporating at least a portion of the solvent carrier to form a dried coating.
7. The method of claim 1, wherein the polymeric material is applied to the surface of the medical device by spraying.
8. The method of claim 1, wherein the polymeric material is applied to the surface of the medical device by immersing the medical device in the polymeric material.
9. The method of claim 1, wherein the medical device is a stent.
10. A method for applying a polymeric coating to a medical device, the method comprising the steps of:
providing a medical device having a surface thereon;
providing a generally tubular member defining a lumen and at least one aperture in fluid communication with the lumen;
applying a polymeric material to the surface of the medical device;
positioning the tubular member proximate the medical device; and releasing a stream of gas through the tool so that it impinges on the surface of the medical device, wherein excess polymeric material is removed from or redistributed on the surface of the medical device.
providing a medical device having a surface thereon;
providing a generally tubular member defining a lumen and at least one aperture in fluid communication with the lumen;
applying a polymeric material to the surface of the medical device;
positioning the tubular member proximate the medical device; and releasing a stream of gas through the tool so that it impinges on the surface of the medical device, wherein excess polymeric material is removed from or redistributed on the surface of the medical device.
11. The method of claim 10, wherein the at least one aperture is a hole.
12. The method of claim 10, wherein the at least one aperture is a slot.
13. The method of claim 10, wherein the polymeric material includes a solvent carrier.
14. The method of claim 13, further including the step of evaporating at least a portion of the solvent carrier to form a dried coating.
15. The method of claim 10, wherein the polymeric material is applied to the surface of the medical device by spraying.
16. The method of claim 10, wherein the polymeric material is applied to the surface of the medical device by immersing the medical device in the polymeric material.
17. The method of claim 10, wherein the medical device is a stent.
18. A method of applying a polymeric coating to a stent, the method comprising the steps of:
providing a stent having a surface generally defined by a plurality of interconnecting struts with open interstitial spaces therebetween;
the stent including a lumen extending through at least a portion thereof;
providing a generally tubular member defining a lumen and at least one aperture in fluid communication with the lumen;
applying a polymeric material to the surface of the stent;
positioning the tubular member inside the lumen of the stent; and releasing a compressed gas to atmosphere through the tubular member;
wherein, gas exits the tubular member through the at least one aperture and travels through the interstitial spaces of the stent;
providing a stent having a surface generally defined by a plurality of interconnecting struts with open interstitial spaces therebetween;
the stent including a lumen extending through at least a portion thereof;
providing a generally tubular member defining a lumen and at least one aperture in fluid communication with the lumen;
applying a polymeric material to the surface of the stent;
positioning the tubular member inside the lumen of the stent; and releasing a compressed gas to atmosphere through the tubular member;
wherein, gas exits the tubular member through the at least one aperture and travels through the interstitial spaces of the stent;
19. The method of claim 18, wherein the at least one aperture is a hole.
20. The method of claim 18, wherein the at least one aperture is a slot.
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PCT/US2000/011273 WO2000066189A2 (en) | 1999-05-03 | 2000-04-26 | Medical device coating method and coated devices |
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EP (1) | EP1185380B1 (en) |
JP (1) | JP2003500087A (en) |
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CA (1) | CA2370824A1 (en) |
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Families Citing this family (191)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8728143B2 (en) | 1996-06-06 | 2014-05-20 | Biosensors International Group, Ltd. | Endoprosthesis deployment system for treating vascular bifurcations |
US7238197B2 (en) | 2000-05-30 | 2007-07-03 | Devax, Inc. | Endoprosthesis deployment system for treating vascular bifurcations |
US7686846B2 (en) | 1996-06-06 | 2010-03-30 | Devax, Inc. | Bifurcation stent and method of positioning in a body lumen |
US7223571B2 (en) * | 1998-04-02 | 2007-05-29 | The Board Of Regents Of The Universtiy Of Oklahoma | Targeted glycosaminoglycan polymers by polymer grafting and methods of making and using same |
US20060188966A1 (en) * | 1998-04-02 | 2006-08-24 | Deangelis Paul L | Natural, chimeric and hybrid glycosaminoglycan polymers and methods of making and using same |
US8088604B2 (en) | 1998-04-02 | 2012-01-03 | The Board Of Regents Of The University Of Oklahoma | Production of defined monodisperse heparosan polymers and unnatural polymers with polysaccharide synthases |
US20080108110A1 (en) * | 1998-04-02 | 2008-05-08 | Deangelis Paul L | Targeted glycosaminoglycan polymers by polymer grafting and methods of making and using same |
US20030040790A1 (en) | 1998-04-15 | 2003-02-27 | Furst Joseph G. | Stent coating |
WO1999055396A1 (en) * | 1998-04-27 | 1999-11-04 | Surmodics, Inc. | Bioactive agent release coating |
AU5054499A (en) * | 1998-07-21 | 2000-02-14 | Biocompatibles Limited | Coating |
US8070796B2 (en) * | 1998-07-27 | 2011-12-06 | Icon Interventional Systems, Inc. | Thrombosis inhibiting graft |
US7967855B2 (en) | 1998-07-27 | 2011-06-28 | Icon Interventional Systems, Inc. | Coated medical device |
US20040197868A1 (en) * | 2001-05-08 | 2004-10-07 | Deangelis Paul L. | Heparin/heparosan synthase from P. multocida, soluble and single action catalysts thereof and methods of making and using same |
US6156373A (en) | 1999-05-03 | 2000-12-05 | Scimed Life Systems, Inc. | Medical device coating methods and devices |
IT1307263B1 (en) * | 1999-08-05 | 2001-10-30 | Sorin Biomedica Cardio Spa | ANGIOPLASTIC STENT WITH RESTENOSIS ANTAGONIST ACTION, RELATED KIT AND COMPONENTS. |
US6273901B1 (en) * | 1999-08-10 | 2001-08-14 | Scimed Life Systems, Inc. | Thrombosis filter having a surface treatment |
US6379383B1 (en) | 1999-11-19 | 2002-04-30 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal device exhibiting improved endothelialization and method of manufacture thereof |
US6981987B2 (en) | 1999-12-22 | 2006-01-03 | Ethicon, Inc. | Removable stent for body lumens |
US7169187B2 (en) * | 1999-12-22 | 2007-01-30 | Ethicon, Inc. | Biodegradable stent |
US6494908B1 (en) | 1999-12-22 | 2002-12-17 | Ethicon, Inc. | Removable stent for body lumens |
US6338739B1 (en) * | 1999-12-22 | 2002-01-15 | Ethicon, Inc. | Biodegradable stent |
AU2001229631A1 (en) * | 2000-01-19 | 2001-07-31 | Johns Hopkins University | Method and apparatus for coating an endoprosthesis |
US6589968B2 (en) | 2001-02-13 | 2003-07-08 | Kosan Biosciences, Inc. | Epothilone compounds and methods for making and using the same |
US20100125329A1 (en) * | 2000-11-02 | 2010-05-20 | Zhi Cheng Lin | Pseudoelastic stents having a drug coating and a method of producing the same |
US6602272B2 (en) | 2000-11-02 | 2003-08-05 | Advanced Cardiovascular Systems, Inc. | Devices configured from heat shaped, strain hardened nickel-titanium |
US7976648B1 (en) | 2000-11-02 | 2011-07-12 | Abbott Cardiovascular Systems Inc. | Heat treatment for cold worked nitinol to impart a shape setting capability without eventually developing stress-induced martensite |
WO2002038080A2 (en) | 2000-11-07 | 2002-05-16 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal stent, self-fupporting endoluminal graft and methods of making same |
US6855161B2 (en) | 2000-12-27 | 2005-02-15 | Advanced Cardiovascular Systems, Inc. | Radiopaque nitinol alloys for medical devices |
US7504125B1 (en) | 2001-04-27 | 2009-03-17 | Advanced Cardiovascular Systems, Inc. | System and method for coating implantable devices |
US20030215564A1 (en) * | 2001-01-18 | 2003-11-20 | Heller Phillip F. | Method and apparatus for coating an endoprosthesis |
US6893859B2 (en) | 2001-02-13 | 2005-05-17 | Kosan Biosciences, Inc. | Epothilone derivatives and methods for making and using the same |
US6913762B2 (en) * | 2001-04-25 | 2005-07-05 | Mayo Foundation For Medical Education And Research | Stent having non-woven framework containing cells |
US20020161376A1 (en) * | 2001-04-27 | 2002-10-31 | Barry James J. | Method and system for delivery of coated implants |
US8580290B2 (en) * | 2001-05-08 | 2013-11-12 | The Board Of Regents Of The University Of Oklahoma | Heparosan-based biomaterials and coatings and methods of production and use thereof |
AU2002256501B2 (en) * | 2001-05-08 | 2008-05-29 | The Board Of Regents Of The University Of Oklahoma | Heparin/heparosan synthase and methods of making and using same |
US7923055B2 (en) * | 2001-05-11 | 2011-04-12 | Exogenesis Corporation | Method of manufacturing a drug delivery system |
US8889169B2 (en) * | 2001-05-11 | 2014-11-18 | Exogenesis Corporation | Drug delivery system and method of manufacturing thereof |
US7666462B2 (en) * | 2001-05-11 | 2010-02-23 | Exogenesis Corporation | Method of controlling a drug release rate |
US6605154B1 (en) * | 2001-05-31 | 2003-08-12 | Advanced Cardiovascular Systems, Inc. | Stent mounting device |
US20030044514A1 (en) * | 2001-06-13 | 2003-03-06 | Richard Robert E. | Using supercritical fluids to infuse therapeutic on a medical device |
US6695920B1 (en) * | 2001-06-27 | 2004-02-24 | Advanced Cardiovascular Systems, Inc. | Mandrel for supporting a stent and a method of using the mandrel to coat a stent |
US6572644B1 (en) * | 2001-06-27 | 2003-06-03 | Advanced Cardiovascular Systems, Inc. | Stent mounting device and a method of using the same to coat a stent |
US8741378B1 (en) * | 2001-06-27 | 2014-06-03 | Advanced Cardiovascular Systems, Inc. | Methods of coating an implantable device |
US6565659B1 (en) * | 2001-06-28 | 2003-05-20 | Advanced Cardiovascular Systems, Inc. | Stent mounting assembly and a method of using the same to coat a stent |
US6673154B1 (en) * | 2001-06-28 | 2004-01-06 | Advanced Cardiovascular Systems, Inc. | Stent mounting device to coat a stent |
US6527863B1 (en) | 2001-06-29 | 2003-03-04 | Advanced Cardiovascular Systems, Inc. | Support device for a stent and a method of using the same to coat a stent |
US6589591B1 (en) * | 2001-07-10 | 2003-07-08 | Baylor College Of Medicine | Method for treating medical devices using glycerol and an antimicrobial agent |
US20030088307A1 (en) * | 2001-11-05 | 2003-05-08 | Shulze John E. | Potent coatings for stents |
DE10200388A1 (en) * | 2002-01-08 | 2003-07-24 | Translumina Gmbh | coating system |
US7105198B2 (en) * | 2002-01-14 | 2006-09-12 | Medtronic Vascular, Inc. | Method for coating stent |
US8685427B2 (en) | 2002-07-31 | 2014-04-01 | Boston Scientific Scimed, Inc. | Controlled drug delivery |
US8133501B2 (en) | 2002-02-08 | 2012-03-13 | Boston Scientific Scimed, Inc. | Implantable or insertable medical devices for controlled drug delivery |
US7097850B2 (en) | 2002-06-18 | 2006-08-29 | Surmodics, Inc. | Bioactive agent release coating and controlled humidity method |
US20040138695A1 (en) * | 2002-06-18 | 2004-07-15 | Shu-Tung Li | Coatings of implants |
US8920826B2 (en) | 2002-07-31 | 2014-12-30 | Boston Scientific Scimed, Inc. | Medical imaging reference devices |
US8016881B2 (en) | 2002-07-31 | 2011-09-13 | Icon Interventional Systems, Inc. | Sutures and surgical staples for anastamoses, wound closures, and surgical closures |
US20040024448A1 (en) | 2002-08-05 | 2004-02-05 | Chang James W. | Thermoplastic fluoropolymer-coated medical devices |
US6818063B1 (en) * | 2002-09-24 | 2004-11-16 | Advanced Cardiovascular Systems, Inc. | Stent mandrel fixture and method for minimizing coating defects |
US7776381B1 (en) * | 2002-09-26 | 2010-08-17 | Advanced Cardiovascular Systems, Inc. | Stent mandrel fixture and method for reducing coating defects |
EP1549248A4 (en) | 2002-09-26 | 2015-11-25 | Advanced Bio Prosthetic Surfac | High strength vacuum deposited nitionol alloy films, medical thin film graft materials and method of making same |
US7125577B2 (en) * | 2002-09-27 | 2006-10-24 | Surmodics, Inc | Method and apparatus for coating of substrates |
USRE40722E1 (en) | 2002-09-27 | 2009-06-09 | Surmodics, Inc. | Method and apparatus for coating of substrates |
US7192484B2 (en) * | 2002-09-27 | 2007-03-20 | Surmodics, Inc. | Advanced coating apparatus and method |
US7335265B1 (en) | 2002-10-08 | 2008-02-26 | Advanced Cardiovascular Systems Inc. | Apparatus and method for coating stents |
KR100966667B1 (en) | 2002-11-07 | 2010-06-29 | 코산 바이오사이언시즈, 인코포레이티드 | Trans-9,10-dehydroepothilone c and d, analogs thereof and methods of making the same |
DE60231843D1 (en) | 2002-11-08 | 2009-05-14 | Jacques Seguin | ENDOPROTHESIS FOR VESSEL FORKING |
US7416609B1 (en) * | 2002-11-25 | 2008-08-26 | Advanced Cardiovascular Systems, Inc. | Support assembly for a stent |
US7074276B1 (en) | 2002-12-12 | 2006-07-11 | Advanced Cardiovascular Systems, Inc. | Clamp mandrel fixture and a method of using the same to minimize coating defects |
US7628859B1 (en) * | 2002-12-27 | 2009-12-08 | Advanced Cardiovascular Systems, Inc. | Mounting assembly for a stent and a method of using the same to coat a stent |
ES2354605T3 (en) * | 2003-02-21 | 2011-03-16 | Sorin Biomedica Cardio S.R.L. | STENTS PRODUCTION PROCEDURE AND THE CORRESPONDING STENT. |
US7354480B1 (en) * | 2003-02-26 | 2008-04-08 | Advanced Cardiovascular Systems, Inc. | Stent mandrel fixture and system for reducing coating defects |
US7175607B2 (en) * | 2003-03-06 | 2007-02-13 | Advanced Cardiovascular Systems, Inc. | Catheter balloon liner with variable thickness and method for making same |
EP1608319A4 (en) | 2003-04-03 | 2007-02-28 | Univ California | Improved inhibitors for the soluble epoxide hydrolase |
US7942892B2 (en) | 2003-05-01 | 2011-05-17 | Abbott Cardiovascular Systems Inc. | Radiopaque nitinol embolic protection frame |
US7279174B2 (en) * | 2003-05-08 | 2007-10-09 | Advanced Cardiovascular Systems, Inc. | Stent coatings comprising hydrophilic additives |
US7323209B1 (en) | 2003-05-15 | 2008-01-29 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for coating stents |
US20040247775A1 (en) * | 2003-06-06 | 2004-12-09 | Boulais Dennis R. | Positive displacement coating deposition apparatus and method |
US20050058768A1 (en) * | 2003-09-16 | 2005-03-17 | Eyal Teichman | Method for coating prosthetic stents |
US7055237B2 (en) * | 2003-09-29 | 2006-06-06 | Medtronic Vascular, Inc. | Method of forming a drug eluting stent |
US7198675B2 (en) | 2003-09-30 | 2007-04-03 | Advanced Cardiovascular Systems | Stent mandrel fixture and method for selectively coating surfaces of a stent |
US8042485B1 (en) | 2003-12-30 | 2011-10-25 | Advanced Cardiovascular Systems, Inc. | Stent mandrel fixture and method for coating stents |
US7211108B2 (en) | 2004-01-23 | 2007-05-01 | Icon Medical Corp. | Vascular grafts with amphiphilic block copolymer coatings |
US20050196518A1 (en) * | 2004-03-03 | 2005-09-08 | Stenzel Eric B. | Method and system for making a coated medical device |
US6979473B2 (en) * | 2004-03-15 | 2005-12-27 | Boston Scientific Scimed, Inc. | Method for fine bore orifice spray coating of medical devices and pre-filming atomization |
JP2007532484A (en) | 2004-03-16 | 2007-11-15 | ザ・レジェンツ・オブ・ザ・ユニバーシティ・オブ・カリフォルニア | Method for alleviating nephropathy using an inhibitor of soluble epoxide hydrolase and epoxyeicosanoids |
US8349388B1 (en) | 2004-03-18 | 2013-01-08 | Advanced Cardiovascular Systems, Inc. | Method of coating a stent |
AU2005231417A1 (en) * | 2004-04-02 | 2005-10-20 | Baylor College Of Medicine | Novel modification of medical prostheses |
US8709469B2 (en) | 2004-06-30 | 2014-04-29 | Abbott Cardiovascular Systems Inc. | Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device |
CN101084216B (en) * | 2004-10-20 | 2011-09-14 | 加利福尼亚大学董事会 | Inhibitors for the soluble epoxide hydrolase |
US7958840B2 (en) * | 2004-10-27 | 2011-06-14 | Surmodics, Inc. | Method and apparatus for coating of substrates |
US7892592B1 (en) | 2004-11-30 | 2011-02-22 | Advanced Cardiovascular Systems, Inc. | Coating abluminal surfaces of stents and other implantable medical devices |
US7540995B2 (en) | 2005-03-03 | 2009-06-02 | Icon Medical Corp. | Process for forming an improved metal alloy stent |
WO2006110197A2 (en) | 2005-03-03 | 2006-10-19 | Icon Medical Corp. | Polymer biodegradable medical device |
US9107899B2 (en) | 2005-03-03 | 2015-08-18 | Icon Medical Corporation | Metal alloys for medical devices |
US7396556B2 (en) * | 2005-03-25 | 2008-07-08 | Boston Scientific Scimed, Inc. | Method of coating a medical appliance utilizing vibration |
US8574259B2 (en) | 2005-05-10 | 2013-11-05 | Lifescreen Sciences Llc | Intravascular filter with drug reservoir |
JP2006334512A (en) * | 2005-06-02 | 2006-12-14 | Honda Motor Co Ltd | Coating method of coating film protective layer, and its coating nozzle |
US7823533B2 (en) | 2005-06-30 | 2010-11-02 | Advanced Cardiovascular Systems, Inc. | Stent fixture and method for reducing coating defects |
US7735449B1 (en) | 2005-07-28 | 2010-06-15 | Advanced Cardiovascular Systems, Inc. | Stent fixture having rounded support structures and method for use thereof |
US20070048452A1 (en) * | 2005-09-01 | 2007-03-01 | James Feng | Apparatus and method for field-injection electrostatic spray coating of medical devices |
EP1971594A2 (en) * | 2005-11-21 | 2008-09-24 | Biogen Idec MA Inc. | Substituted pyrazalones |
US7867547B2 (en) | 2005-12-19 | 2011-01-11 | Advanced Cardiovascular Systems, Inc. | Selectively coating luminal surfaces of stents |
US8039475B2 (en) | 2006-02-27 | 2011-10-18 | Vertex Pharmaceuticals Incorporated | Co-crystals and pharmaceutical compositions comprising the same |
AR059826A1 (en) | 2006-03-13 | 2008-04-30 | Univ California | UREA INHIBITORS CONFORMATIONALLY RESTRICTED OF SOLUBLE HYDROLASSE EPOXIDE |
US20070259116A1 (en) * | 2006-05-02 | 2007-11-08 | Boston Scientific Scimed, Inc. | Partially coated workpiece and method of making same |
US8003156B2 (en) | 2006-05-04 | 2011-08-23 | Advanced Cardiovascular Systems, Inc. | Rotatable support elements for stents |
US8304012B2 (en) | 2006-05-04 | 2012-11-06 | Advanced Cardiovascular Systems, Inc. | Method for drying a stent |
US7985441B1 (en) | 2006-05-04 | 2011-07-26 | Yiwen Tang | Purification of polymers for coating applications |
EP2020956A2 (en) * | 2006-05-26 | 2009-02-11 | Nanyang Technological University | Implantable article, method of forming same and method for reducing thrombogenicity |
US8097291B2 (en) * | 2006-06-05 | 2012-01-17 | Boston Scientific Scimed, Inc. | Methods for coating workpieces |
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 |
US8017237B2 (en) | 2006-06-23 | 2011-09-13 | Abbott Cardiovascular Systems, Inc. | Nanoshells on polymers |
US9265865B2 (en) * | 2006-06-30 | 2016-02-23 | Boston Scientific Scimed, Inc. | Stent having time-release indicator |
US8114466B2 (en) * | 2007-01-03 | 2012-02-14 | Boston Scientific Scimed, Inc. | Methods of applying coating to the inside surface of a stent |
US8814930B2 (en) | 2007-01-19 | 2014-08-26 | Elixir Medical Corporation | Biodegradable endoprosthesis and methods for their fabrication |
US20080189928A1 (en) * | 2007-02-12 | 2008-08-14 | Medtronic Vascular, Inc. | Stent Ring Surface Formation |
ES2379905T3 (en) | 2007-02-27 | 2012-05-04 | Vertex Pharmceuticals Incorporated | Co-crystals and pharmaceutical compositions comprising them |
US8003157B2 (en) | 2007-06-15 | 2011-08-23 | Abbott Cardiovascular Systems Inc. | System and method for coating a stent |
US8677650B2 (en) * | 2007-06-15 | 2014-03-25 | Abbott Cardiovascular Systems Inc. | Methods and devices for drying coated stents |
US7897195B2 (en) * | 2007-06-15 | 2011-03-01 | Abbott Cardiovascular Systems Inc. | Devices for coating stents |
US8048441B2 (en) | 2007-06-25 | 2011-11-01 | Abbott Cardiovascular Systems, Inc. | Nanobead releasing medical devices |
GB0713871D0 (en) * | 2007-07-17 | 2007-08-29 | Johnson William N H | Flood barrier or the like |
WO2009020960A1 (en) | 2007-08-06 | 2009-02-12 | The Regents Of The University Of California | Preparation of novel 1,3-substituted ureas as inhibitors of soluble epoxide hydrolase |
US8333795B2 (en) * | 2007-08-27 | 2012-12-18 | Boston Scientific Scimed, Inc. | Bulging balloon for bifurcation catheter assembly and methods |
US20090069878A1 (en) * | 2007-08-27 | 2009-03-12 | Boston Scientific Scimed, Inc. | Bifurcation post-dilatation balloon and methods |
CL2008002549A1 (en) | 2007-08-30 | 2010-09-03 | Vertex Pharma | Cocrystal comprising vx-950 and a cocrystal former selected from 3-methoxy-4-hydroxybenzoic acid, 2,4-dihydroxybenzoic acid and 2,5-dihydroxybenzoic acid; Preparation method; Pharmaceutical composition comprising cocrystal, useful as an antiviral agent in the treatment of hcv. |
US8661630B2 (en) | 2008-05-21 | 2014-03-04 | Abbott Cardiovascular Systems Inc. | Coating comprising an amorphous primer layer and a semi-crystalline reservoir layer |
WO2009076200A2 (en) | 2007-12-07 | 2009-06-18 | Vertex Pharmaceuticals Incorporated | Solid forms of 1-ethyl-3-(5-(5-fluoropyridin-3-yl)-7-(pyrimidin-2-yl)-1h-benzo[d]imidazol-2-yl)urea |
US7998524B2 (en) | 2007-12-10 | 2011-08-16 | Abbott Cardiovascular Systems Inc. | Methods to improve adhesion of polymer coatings over stents |
US8361538B2 (en) | 2007-12-19 | 2013-01-29 | Abbott Laboratories | Methods for applying an application material to an implantable device |
US8211489B2 (en) * | 2007-12-19 | 2012-07-03 | Abbott Cardiovascular Systems, Inc. | Methods for applying an application material to an implantable device |
US9925209B2 (en) | 2008-03-19 | 2018-03-27 | The Board Of Regents Of The University Of Oklahoma | Heparosan-polypeptide and heparosan-polynucleotide drug conjugates and methods of making and using same |
US9687559B2 (en) | 2008-03-19 | 2017-06-27 | The Board Of Regents Of The University Of Oklahoma | Heparosan polymers and methods of making and using same for the enhancement of therapeutics |
US9364349B2 (en) | 2008-04-24 | 2016-06-14 | Surmodics, Inc. | Coating application system with shaped mandrel |
US8206635B2 (en) | 2008-06-20 | 2012-06-26 | Amaranth Medical Pte. | Stent fabrication via tubular casting processes |
US10898620B2 (en) | 2008-06-20 | 2021-01-26 | Razmodics Llc | Composite stent having multi-axial flexibility and method of manufacture thereof |
US8206636B2 (en) | 2008-06-20 | 2012-06-26 | Amaranth Medical Pte. | Stent fabrication via tubular casting processes |
EP2323708A4 (en) * | 2008-08-07 | 2015-11-18 | Exogenesis Corp | Drug delivery system and method of munufacturing thereof |
JP5878369B2 (en) * | 2008-08-07 | 2016-03-08 | エクソジェネシス コーポレーション | Medical device for bone implant and method of manufacturing the device |
US8114429B2 (en) | 2008-09-15 | 2012-02-14 | Cv Ingenuity Corp. | Local delivery of water-soluble or water-insoluble therapeutic agents to the surface of body lumens |
US9198968B2 (en) | 2008-09-15 | 2015-12-01 | The Spectranetics Corporation | Local delivery of water-soluble or water-insoluble therapeutic agents to the surface of body lumens |
US20100135949A1 (en) * | 2008-12-01 | 2010-06-03 | Becton, Dickinson And Company | Antimicrobial compositions |
CA2752544A1 (en) | 2009-02-13 | 2010-08-19 | Vertex Pharmaceuticals Incorporated | Solid forms of 2-(2, 4-difluorophenyl)-6-(1-(2,6-difluorophenyl)ureido)nicotinamide |
AU2010261804A1 (en) | 2009-06-17 | 2012-01-12 | Dot Gmbh | Method and device for coating catheters or balloon catheters |
WO2012054093A2 (en) | 2010-01-29 | 2012-04-26 | The Regents Of The University Of California | Acyl piperidine inhibitors of soluble epoxide hydrolase |
US8398916B2 (en) | 2010-03-04 | 2013-03-19 | Icon Medical Corp. | Method for forming a tubular medical device |
US8685433B2 (en) | 2010-03-31 | 2014-04-01 | Abbott Cardiovascular Systems Inc. | Absorbable coating for implantable device |
EP2663557B1 (en) | 2011-01-14 | 2015-05-27 | Vertex Pharmaceuticals Incorporated | Pyrimidine gyrase and topoisomerase iv inhibitors |
ES2705923T3 (en) | 2011-01-14 | 2019-03-27 | Spero Trinem Inc | Solid forms of gyrase inhibitor (R) -1-ethyl-3- [6-fluoro-5- [2- (1-hydroxy-1-methyl-ethyl) pyrimidin-5-yl] -7- (tetrahydrofuran-2) -yl) -1H-benzimidazol-2-yl] urea |
WO2012112570A1 (en) | 2011-02-14 | 2012-08-23 | The Regents Of The University Of California | SORAFENIB DERIVATIVES AS sEH INHIBITORS |
US9187953B2 (en) | 2011-03-23 | 2015-11-17 | Rytec Corporation | Side column configuration for overhead roll-up door assemblies |
CN103702994B (en) | 2011-06-20 | 2016-03-23 | 沃泰克斯药物股份有限公司 | The phosphoric acid ester of gyrase and topoisomerase enzyme inhibitor |
EP2809650B1 (en) | 2012-02-01 | 2018-04-11 | The Regents of The University of California | Acyl piperidine inhibitors of soluble epoxide hydrolase |
TR201802761T4 (en) | 2012-03-30 | 2018-03-21 | Univ Oklahoma | High molecular weight heparosan polymers and methods for their production and use. |
US9352119B2 (en) | 2012-05-15 | 2016-05-31 | Becton, Dickinson And Company | Blood control IV catheter with antimicrobial properties |
JP6549482B2 (en) | 2012-06-01 | 2019-07-24 | サーモディクス,インコーポレイテッド | Device and method for coating a balloon catheter |
US9827401B2 (en) | 2012-06-01 | 2017-11-28 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
US9956385B2 (en) * | 2012-06-28 | 2018-05-01 | The Spectranetics Corporation | Post-processing of a medical device to control morphology and mechanical properties |
TWI595002B (en) | 2012-07-18 | 2017-08-11 | 思沛羅三南公司 | Solid forms of (r)-2-(5-(2-(3-ethylureido)-6-fluoro-7-(tetrahydrofuran-2-yl)-1h-benzo[d]imidazol-5-yl)pyrimidin-2-yl)propan-2-yl dihydrogen phosphate and salts thereof |
US9579486B2 (en) | 2012-08-22 | 2017-02-28 | Becton, Dickinson And Company | Blood control IV catheter with antimicrobial properties |
US11090468B2 (en) | 2012-10-25 | 2021-08-17 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
US9283350B2 (en) | 2012-12-07 | 2016-03-15 | Surmodics, Inc. | Coating apparatus and methods |
US9695323B2 (en) | 2013-02-13 | 2017-07-04 | Becton, Dickinson And Company | UV curable solventless antimicrobial compositions |
US9750928B2 (en) | 2013-02-13 | 2017-09-05 | Becton, Dickinson And Company | Blood control IV catheter with stationary septum activator |
US9750927B2 (en) | 2013-03-11 | 2017-09-05 | Becton, Dickinson And Company | Blood control catheter with antimicrobial needle lube |
US9327095B2 (en) | 2013-03-11 | 2016-05-03 | Becton, Dickinson And Company | Blood control catheter with antimicrobial needle lube |
US9545301B2 (en) | 2013-03-15 | 2017-01-17 | Covidien Lp | Coated medical devices and methods of making and using same |
US9320592B2 (en) | 2013-03-15 | 2016-04-26 | Covidien Lp | Coated medical devices and methods of making and using same |
DK3424920T3 (en) | 2013-10-17 | 2020-06-08 | Vertex Pharma | CO CRYSTALS OF (S) -N-METHYL-8- (1 - ((2'-METHYL- [4,5'-BIPYRIMIDIN] -6-YL) AMINO) PROPAN-2-YL) QUINOLIN-4-CARBOXAMIDE AND DEUTERATED DERIVATIVES THEREOF AS DNA-PK INHIBITORS |
US9668890B2 (en) | 2013-11-22 | 2017-06-06 | Covidien Lp | Anti-thrombogenic medical devices and methods |
US9855577B1 (en) * | 2014-01-23 | 2018-01-02 | Sio2 Medical Products, Inc. | Needle siliconization with controlled positive pressure gas flow |
US10525171B2 (en) | 2014-01-24 | 2020-01-07 | The Spectranetics Corporation | Coatings for medical devices |
US10376686B2 (en) | 2014-04-23 | 2019-08-13 | Becton, Dickinson And Company | Antimicrobial caps for medical connectors |
US9789279B2 (en) | 2014-04-23 | 2017-10-17 | Becton, Dickinson And Company | Antimicrobial obturator for use with vascular access devices |
US9675793B2 (en) | 2014-04-23 | 2017-06-13 | Becton, Dickinson And Company | Catheter tubing with extraluminal antimicrobial coating |
BR112016030273A8 (en) | 2014-06-24 | 2021-05-18 | Icon Medical Corp | medical device and method of forming said device |
US10232088B2 (en) | 2014-07-08 | 2019-03-19 | Becton, Dickinson And Company | Antimicrobial coating forming kink resistant feature on a vascular access device |
US9895243B2 (en) | 2014-07-17 | 2018-02-20 | W. L. Gore & Associates, Inc. | Stent having adjacent elements connected by narrow flexible webs |
US9259339B1 (en) | 2014-08-15 | 2016-02-16 | Elixir Medical Corporation | Biodegradable endoprostheses and methods of their fabrication |
US9730819B2 (en) | 2014-08-15 | 2017-08-15 | Elixir Medical Corporation | Biodegradable endoprostheses and methods of their fabrication |
US9480588B2 (en) | 2014-08-15 | 2016-11-01 | Elixir Medical Corporation | Biodegradable endoprostheses and methods of their fabrication |
US9855156B2 (en) | 2014-08-15 | 2018-01-02 | Elixir Medical Corporation | Biodegradable endoprostheses and methods of their fabrication |
US9789228B2 (en) | 2014-12-11 | 2017-10-17 | Covidien Lp | Antimicrobial coatings for medical devices and processes for preparing such coatings |
US10493244B2 (en) | 2015-10-28 | 2019-12-03 | Becton, Dickinson And Company | Extension tubing strain relief |
US11766506B2 (en) | 2016-03-04 | 2023-09-26 | Mirus Llc | Stent device for spinal fusion |
CN113143536B (en) | 2016-05-16 | 2022-08-30 | 万能医药公司 | Opening support |
US11622872B2 (en) | 2016-05-16 | 2023-04-11 | Elixir Medical Corporation | Uncaging stent |
US11628466B2 (en) | 2018-11-29 | 2023-04-18 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
US11819590B2 (en) | 2019-05-13 | 2023-11-21 | Surmodics, Inc. | Apparatus and methods for coating medical devices |
Family Cites Families (85)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3946125A (en) * | 1970-10-24 | 1976-03-23 | Metallgesellschaft Aktiengesellschaft | Method for internally coating ducts with synthetic resin |
US4391797A (en) * | 1977-01-05 | 1983-07-05 | The Children's Hospital Medical Center | Systems for the controlled release of macromolecules |
US4487808A (en) * | 1982-04-22 | 1984-12-11 | Astra Meditec Aktiebolag | Medical article having a hydrophilic coating |
SE430696B (en) * | 1982-04-22 | 1983-12-05 | Astra Meditec Ab | PROCEDURE FOR THE PREPARATION OF A HYDROPHILIC COATING AND ANY PROCEDURE MANUFACTURED MEDICAL ARTICLE |
US4842575A (en) * | 1984-01-30 | 1989-06-27 | Meadox Medicals, Inc. | Method for forming impregnated synthetic vascular grafts |
SE452404B (en) * | 1984-02-03 | 1987-11-30 | Medinvent Sa | MULTILAYER PROTEST MATERIAL AND PROCEDURE FOR ITS MANUFACTURING |
US4923464A (en) * | 1985-09-03 | 1990-05-08 | Becton, Dickinson And Company | Percutaneously deliverable intravascular reconstruction prosthesis |
US5102417A (en) * | 1985-11-07 | 1992-04-07 | Expandable Grafts Partnership | Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft |
EP0257091B1 (en) * | 1986-02-24 | 1993-07-28 | Robert E. Fischell | An intravascular stent and percutaneous insertion system |
US4893623A (en) * | 1986-12-09 | 1990-01-16 | Advanced Surgical Intervention, Inc. | Method and apparatus for treating hypertrophy of the prostate gland |
US5092885A (en) * | 1987-02-12 | 1992-03-03 | The Government Of The United States Of America As Represented By The Secretary Of The Department Of Health And Human Services | Peptides with laminin activity |
NL8701337A (en) * | 1987-06-09 | 1989-01-02 | Sentron V O F | SUBSTRATE PROVIDED WITH A BLOOD COMPATIBLE SURFACE OBTAINED BY COUPLING WITH THE SURFACE OF A PHYSIOLOGICALLY ACTIVE SUBSTANCE WITH AN INHIBITORY INFLUENCE ON THE FORMATION OF BLOOD CLOTS AND / OR CONTAINED FROM HARMFOLIC CIRCULARS. |
US5527337A (en) * | 1987-06-25 | 1996-06-18 | Duke University | Bioabsorbable stent and method of making the same |
JPH088933B2 (en) * | 1987-07-10 | 1996-01-31 | 日本ゼオン株式会社 | Catheter |
US5019096A (en) * | 1988-02-11 | 1991-05-28 | Trustees Of Columbia University In The City Of New York | Infection-resistant compositions, medical devices and surfaces and methods for preparing and using same |
DE68922497T2 (en) * | 1988-08-24 | 1995-09-14 | Marvin J Slepian | ENDOLUMINAL SEAL WITH BISDEGRADABLE POLYMERS. |
WO1990013332A1 (en) * | 1989-05-11 | 1990-11-15 | Cedars-Sinai Medical Center | Stent with sustained drug delivery |
US4994071A (en) * | 1989-05-22 | 1991-02-19 | Cordis Corporation | Bifurcating stent apparatus and method |
AU6747790A (en) * | 1989-11-13 | 1991-06-13 | President And Fellows Of Harvard College | Extraluminal regulation of the growth and repair of tubular structures in vivo |
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 |
US5192744A (en) * | 1990-01-12 | 1993-03-09 | Northwestern University | Method of inhibiting angiogenesis of tumors |
DK0512071T3 (en) * | 1990-01-25 | 1996-11-25 | Childrens Hospital | Methods and compositions for inhibiting angiogenesis |
US5545208A (en) * | 1990-02-28 | 1996-08-13 | Medtronic, Inc. | Intralumenal drug eluting prosthesis |
DE69110787T2 (en) * | 1990-02-28 | 1996-04-04 | Medtronic Inc | INTRALUMINAL PROSTHESIS WITH ACTIVE ELEMENTATION. |
AU7998091A (en) * | 1990-05-17 | 1991-12-10 | Harbor Medical Devices, Inc. | Medical device polymer |
DE69129812T2 (en) * | 1990-07-12 | 1999-02-11 | Sts Biopolymers Inc | ANTITHROMOGIC AND / OR ANTIMICROBIAL COMPOSITION |
EP0470569B1 (en) * | 1990-08-08 | 1995-11-22 | Takeda Chemical Industries, Ltd. | Intravascular embolizing agent containing angiogenesis inhibiting substance |
US5258202A (en) * | 1990-10-02 | 1993-11-02 | The United States Of America As Represented By The Secretary Of Commerce | Methods of making and using improved microporous hollow fibers, the improved hollow fibers and tube bundles constructed of the improved fibers |
US5449372A (en) * | 1990-10-09 | 1995-09-12 | Scimed Lifesystems, Inc. | Temporary stent and methods for use and manufacture |
US5222971A (en) * | 1990-10-09 | 1993-06-29 | Scimed Life Systems, Inc. | Temporary stent and methods for use and manufacture |
US5102402A (en) * | 1991-01-04 | 1992-04-07 | Medtronic, Inc. | Releasable coatings on balloon catheters |
US5324261A (en) * | 1991-01-04 | 1994-06-28 | Medtronic, Inc. | Drug delivery balloon catheter with line of weakness |
AU1579092A (en) * | 1991-02-27 | 1992-10-06 | Nova Pharmaceutical Corporation | Anti-infective and anti-inflammatory releasing systems for medical devices |
US5192308A (en) * | 1991-04-19 | 1993-03-09 | E. I. Du Pont De Nemours And Company | Vascular prosthesis with an elastomer coating |
US6515009B1 (en) * | 1991-09-27 | 2003-02-04 | Neorx Corporation | Therapeutic inhibitor of vascular smooth muscle cells |
US5811447A (en) * | 1993-01-28 | 1998-09-22 | Neorx Corporation | Therapeutic inhibitor of vascular smooth muscle cells |
WO1993006792A1 (en) * | 1991-10-04 | 1993-04-15 | Scimed Life Systems, Inc. | Biodegradable drug delivery vascular stent |
CA2079417C (en) * | 1991-10-28 | 2003-01-07 | Lilip Lau | Expandable stents and method of making same |
US5270047A (en) * | 1991-11-21 | 1993-12-14 | Kauffman Raymond F | Local delivery of dipyridamole for the treatment of proliferative diseases |
EP0643706A1 (en) * | 1991-11-27 | 1995-03-22 | Zynaxis Inc. | Compounds, compositions and methods for binding bio-affecting substances to surface membranes of bio-particles |
CA2086642C (en) * | 1992-01-09 | 2004-06-15 | Randall E. Morris | Method of treating hyperproliferative vascular disease |
CA2087132A1 (en) * | 1992-01-31 | 1993-08-01 | Michael S. Williams | Stent capable of attachment within a body lumen |
FR2688401B1 (en) * | 1992-03-12 | 1998-02-27 | Thierry Richard | EXPANDABLE STENT FOR HUMAN OR ANIMAL TUBULAR MEMBER, AND IMPLEMENTATION TOOL. |
US5282823A (en) * | 1992-03-19 | 1994-02-01 | Medtronic, Inc. | Intravascular radially expandable stent |
US5599352A (en) * | 1992-03-19 | 1997-02-04 | Medtronic, Inc. | Method of making a drug eluting stent |
US5460859A (en) * | 1992-03-23 | 1995-10-24 | Xerox Corporation | Method and system for dip coating an article having large open areas or a multiplicity of apertures |
SE500972C2 (en) * | 1992-03-30 | 1994-10-10 | Moelnlycke Ab | Method and apparatus for manufacturing wound dressings and a wound dressing made by the method |
AU670937B2 (en) * | 1992-04-28 | 1996-08-08 | Wyeth | Method of treating hyperproliferative vascular disease |
DE4214215A1 (en) * | 1992-04-30 | 1993-11-04 | Behringwerke Ag | USE OF INHIBITORS OF PLASMINOGEN ACTIVATORS FOR TREATING INFLAMMATION |
US5383928A (en) * | 1992-06-10 | 1995-01-24 | Emory University | Stent sheath for local drug delivery |
FR2696527B1 (en) * | 1992-10-06 | 1994-12-09 | Aerospatiale | Process device for treating the external and internal surfaces of pipes or the like. |
US5578075B1 (en) * | 1992-11-04 | 2000-02-08 | Daynke Res Inc | Minimally invasive bioactivated endoprosthesis for vessel repair |
US5449382A (en) * | 1992-11-04 | 1995-09-12 | Dayton; Michael P. | Minimally invasive bioactivated endoprosthesis for vessel repair |
US5443458A (en) * | 1992-12-22 | 1995-08-22 | Advanced Cardiovascular Systems, Inc. | Multilayered biodegradable stent and method of manufacture |
EP0604022A1 (en) * | 1992-12-22 | 1994-06-29 | Advanced Cardiovascular Systems, Inc. | Multilayered biodegradable stent and method for its manufacture |
GB9226791D0 (en) * | 1992-12-23 | 1993-02-17 | Biocompatibles Ltd | New materials |
US5419760A (en) * | 1993-01-08 | 1995-05-30 | Pdt Systems, Inc. | Medicament dispensing stent for prevention of restenosis of a blood vessel |
WO1994021308A1 (en) * | 1993-03-18 | 1994-09-29 | Cedars-Sinai Medical Center | Drug incorporating and releasing polymeric coating for bioprosthesis |
US5523092A (en) * | 1993-04-14 | 1996-06-04 | Emory University | Device for local drug delivery and methods for using the same |
US5464650A (en) * | 1993-04-26 | 1995-11-07 | Medtronic, Inc. | Intravascular stent and method |
DE69329831T2 (en) * | 1993-04-28 | 2001-04-19 | Kawasaki Steel Co | METHOD FOR REGULATING ADHESION WHILE STRIPING WITH GAS |
CN100998869A (en) * | 1993-07-19 | 2007-07-18 | 血管技术药物公司 | Anti-angiogene compositions and methods of use |
US5994341A (en) * | 1993-07-19 | 1999-11-30 | Angiogenesis Technologies, Inc. | Anti-angiogenic Compositions and methods for the treatment of arthritis |
EP0711158B2 (en) * | 1993-07-29 | 2008-07-23 | THE GOVERNMENT OF THE UNITED STATES OF AMERICA, as represented by THE SECRETARY, DEPARTMENT OF HEALTH AND HUMAN SERVICES | Method of treating atherosclerosis or restenosis using microtubule stabilizing agent |
US5380299A (en) * | 1993-08-30 | 1995-01-10 | Med Institute, Inc. | Thrombolytic treated intravascular medical device |
GB9415926D0 (en) * | 1994-08-04 | 1994-09-28 | Biocompatibles Ltd | New materials |
US5733303A (en) * | 1994-03-17 | 1998-03-31 | Medinol Ltd. | Flexible expandable stent |
US5611151A (en) * | 1994-06-10 | 1997-03-18 | Busch Co. | Strip cooling, heating, wiping or drying apparatus and associated method |
US5626862A (en) * | 1994-08-02 | 1997-05-06 | Massachusetts Institute Of Technology | Controlled local delivery of chemotherapeutic agents for treating solid tumors |
JP2934153B2 (en) * | 1994-08-05 | 1999-08-16 | ティーディーケイ株式会社 | Photoresist film forming method |
US5637113A (en) * | 1994-12-13 | 1997-06-10 | Advanced Cardiovascular Systems, Inc. | Polymer film for wrapping a stent structure |
EP0810845A2 (en) * | 1995-02-22 | 1997-12-10 | Menlo Care Inc. | Covered expanding mesh stent |
US5702754A (en) * | 1995-02-22 | 1997-12-30 | Meadox Medicals, Inc. | Method of providing a substrate with a hydrophilic coating and substrates, particularly medical devices, provided with such coatings |
HU215881B (en) | 1995-02-27 | 1999-03-29 | General Electric Co. | Lamp collar and discharge lamp with lamp collar |
DE69637527D1 (en) * | 1995-03-01 | 2008-06-26 | Boston Scient Scimed Inc | Longitudinally flexible and expandable stent |
US5605696A (en) * | 1995-03-30 | 1997-02-25 | Advanced Cardiovascular Systems, Inc. | Drug loaded polymeric material and method of manufacture |
US5674242A (en) * | 1995-06-06 | 1997-10-07 | Quanam Medical Corporation | Endoprosthetic device with therapeutic compound |
US5824391A (en) * | 1995-06-06 | 1998-10-20 | The Boeing Company | Appliques to eliminate painted coatings on surfaces having complex curvature |
US5609629A (en) * | 1995-06-07 | 1997-03-11 | Med Institute, Inc. | Coated implantable medical device |
US5958512A (en) * | 1996-12-19 | 1999-09-28 | Avery Dennison Corporation | Method and apparatus for selectively removing or displacing a fluid on a web |
KR100526913B1 (en) * | 1997-02-20 | 2005-11-09 | 쿡 인코포레이티드 | Coated implantable medical device |
US5779732A (en) * | 1997-03-31 | 1998-07-14 | Medtronic, Inc. | Method and apparatus for implanting a film with an exandable stent |
AU5054499A (en) * | 1998-07-21 | 2000-02-14 | Biocompatibles Limited | Coating |
US6156373A (en) | 1999-05-03 | 2000-12-05 | Scimed Life Systems, Inc. | Medical device coating methods and devices |
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US6156373A (en) | 2000-12-05 |
US6322847B1 (en) | 2001-11-27 |
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