US20130046375A1 - Plasma modified medical devices and methods - Google Patents

Plasma modified medical devices and methods Download PDF

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US20130046375A1
US20130046375A1 US13/287,019 US201113287019A US2013046375A1 US 20130046375 A1 US20130046375 A1 US 20130046375A1 US 201113287019 A US201113287019 A US 201113287019A US 2013046375 A1 US2013046375 A1 US 2013046375A1
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plasma
modified
containing molecules
nitrogen
contacting surface
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Meng Chen
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Priority to US13/287,019 priority Critical patent/US20130046375A1/en
Priority to CN201280039960.8A priority patent/CN103748147B/zh
Priority to JP2014526038A priority patent/JP6132106B2/ja
Priority to EP12823725.2A priority patent/EP2744852B1/fr
Priority to PCT/US2012/048116 priority patent/WO2013025317A1/fr
Priority to ES12823725.2T priority patent/ES2663099T3/es
Publication of US20130046375A1 publication Critical patent/US20130046375A1/en
Priority to US14/973,401 priority patent/US9603978B2/en
Priority to US15/457,575 priority patent/US10016533B2/en
Abandoned legal-status Critical Current

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    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/08—Materials for coatings
    • A61L31/10—Macromolecular materials
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    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/28—Materials for coating prostheses
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    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
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    • A61L33/06—Use of macromolecular materials
    • A61L33/068—Use of macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
    • B—PERFORMING OPERATIONS; TRANSPORTING
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    • C23—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; CHEMICAL SURFACE TREATMENT; DIFFUSION TREATMENT OF METALLIC MATERIAL; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL; INHIBITING CORROSION OF METALLIC MATERIAL OR INCRUSTATION IN GENERAL
    • C23C—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; SURFACE TREATMENT OF METALLIC MATERIAL BY DIFFUSION INTO THE SURFACE, BY CHEMICAL CONVERSION OR SUBSTITUTION; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL
    • C23C16/00—Chemical coating by decomposition of gaseous compounds, without leaving reaction products of surface material in the coating, i.e. chemical vapour deposition [CVD] processes
    • C23C16/22—Chemical coating by decomposition of gaseous compounds, without leaving reaction products of surface material in the coating, i.e. chemical vapour deposition [CVD] processes characterised by the deposition of inorganic material, other than metallic material
    • C23C16/30—Deposition of compounds, mixtures or solid solutions, e.g. borides, carbides, nitrides
    • C—CHEMISTRY; METALLURGY
    • C23—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; CHEMICAL SURFACE TREATMENT; DIFFUSION TREATMENT OF METALLIC MATERIAL; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL; INHIBITING CORROSION OF METALLIC MATERIAL OR INCRUSTATION IN GENERAL
    • C23C—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; SURFACE TREATMENT OF METALLIC MATERIAL BY DIFFUSION INTO THE SURFACE, BY CHEMICAL CONVERSION OR SUBSTITUTION; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL
    • C23C16/00—Chemical coating by decomposition of gaseous compounds, without leaving reaction products of surface material in the coating, i.e. chemical vapour deposition [CVD] processes
    • C23C16/56—After-treatment
    • 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
    • A61L2300/20—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials
    • A61L2300/204—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials with nitrogen-containing functional groups, e.g. aminoxides, nitriles, guanidines
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    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
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    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
    • A61L2300/416—Anti-neoplastic or anti-proliferative or anti-restenosis or anti-angiogenic agents, e.g. paclitaxel, sirolimus
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    • A61L2400/00—Materials characterised by their function or physical properties
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Definitions

  • This invention relates to applications and methods for glow discharge plasma coatings for medical devices with improved long-term biocompatibility for clinical practice.
  • the present invention relates implantable medical devices such as stents, catheters, pacemakers, and biosensors, and the like, wherein long-lasting and durable bioactive agents or functional groups are deposited on the device surface through a unique two-step plasma coating process to prevent both restenosis and thrombosis in clinical conditions.
  • the invention also relates to surface treatment of metallic and polymeric biomaterials used for making of medical devices with significantly improved clinical performance and durability.
  • CHD Coronary heart disease
  • a coronary artery stent a small mesh tube made of metal or alloys, functions as a scaffold to prop open blocked arteries in the heart to keep them from re-narrowing (referred to clinically as restenosis).
  • BMS implanted bare metal stents
  • DES drug-eluting stents
  • the coating process consists of three steps including a surface priming process, bio-chemical reaction, and covalent bonding [Orbus Neich Expands Global Sales and Marketing Team. www.orbusneich.com/genous/].
  • the use of two drugs coated on stents to simultaneously minimize both restenosis and thrombosis has been studied recently [Huang et al. J Interv Cardiol, 22 (5): 466-478, 2009].
  • the animal studies showed a significant reduction in restenosis, but whether or not the late stent thrombosis will develop remains unclear.
  • Plasma processes have been widely used in the preparation of biomedical materials with unique performance and in the manufacturing of medical devices [Ratner B D in: Plasma Processing of Polymers, 1997].
  • a new nitrogen-rich plasma-deposited biomaterial as an external coating for stent-grafts can promote healing around the implant after endovascular aneurysm repair [Lerouge et al. Biomaterials, 28(6):1209-1217, 2007].
  • Plasma deposition is a thin film forming process typically occurring in a vacuum chamber, where thin films deposit on the surface of substrates under plasma conditions.
  • monomers are introduced into a plasma reactor and get activated to produce a gaseous complex composed of highly energetic electrons, ions, free radicals and excited monomer molecules, known as the plasma state.
  • plasma deposition many appropriate functional groups, such as amine, hydroxyl, carboxylic acid, useful for the immobilization of bioactive molecules, can be created in the deposited coatings. More importantly, these chemical groups can be put onto almost any material by choosing right monomers and plasma process parameters.
  • Plasma surface treatment has also become a powerful tool in solving surface preparation problems on biomedical materials [Chu et al. Mater Sci Eng, R 36: 143-206, 2002].
  • Oxygen plasmas for example, have been used to increase the attachment of cells to polymer surfaces [Ertel et al. J Biomater Sci Polym Ed, 3:163-183, 1991; Chilkoti et al. Anal Chem, 67: 2883-2891, 1995; Ertel et al. J Biomed Mater Res, 24: 1637-1659, 1990].
  • Plasmas have also been used to introduce amines and amides to polymeric materials for increasing the attachment of cells, and in particular endothelial cells [Griesser et al.
  • U.S. Pat. No. 6,613,432 provides a method of using plasma surface modification to introduce a bioactive layer or coating on the surface of implantable medical devices for improved biocompatibility, such as inhibition of restenosis with stents and attachment of platelets and leukocytes.
  • a bioactive layer or coating on the surface of implantable medical devices for improved biocompatibility, such as inhibition of restenosis with stents and attachment of platelets and leukocytes.
  • certain, often large variations have been observed on the patency of plasma treated stents after implantation, which is believed to be due to the potential instability of surface bioactivity generated by the single-step NH 3 /O 2 plasma surface treatment on bare stainless steel surfaces.
  • the invention provides an implantable medical device having at least one contacting surface for contacting a bodily fluid or tissue, wherein the contacting surface is coated by a two step process of plasma treatment comprising a first step of a plasma deposition process using silicon-containing monomers to provide a uniform and conformal nano-scale plasma coating and a second step of a plasma modification process using a mixture of nitrogen and oxygen molecules.
  • the nitrogen-containing molecules each comprise no more than six atoms, and preferably four or fewer atoms.
  • the nitrogen-containing molecules may include NH 3 , NH 4 , N 2 O, NO, NO 2 and N 2 O 4 .
  • the oxygen-containing molecules may include O 2 and O 3 .
  • the plasma treatment with the nitrogen-containing molecules and the oxygen-containing molecules may be simultaneous.
  • a low temperature plasma process is invented to deposit an ultra-thin (nano-scale) but continuous layer of coating, sufficient to generate the desired abrasion resistance and immobilize the bioactive functional groups created in the subsequent plasma surface treatment to prevent blood clots and restenosis, but thin enough to allow for stent expansion without cracking when delivered into patients.
  • the plasma modified metallic surfaces exhibit the following properties: 1) non-clot formation on the NH 3 /O 2 plasma treated stainless steel (SS) surface, combined with increased apoptosis in smooth muscle cells (SMC), and non-inflammatory responses; 2) a thin trimethylsilane (TMS) coating followed by NH 3 /O 2 plasma surface modification with direct current (DC) plasma which delivers statistically significant increases in coronary artery endothelial cell (EC) attachment without promoting SMC proliferation on SS wafers at 12 weeks after plasma coating, suggesting formations of stable and durable bioactive surfaces; 3) a stainless steel stent coated with the two-step plasma coating with DC plasma which exhibits significantly less intimal hyperplasia than untreated controls in swine arteries; 4) surface bound NO functional groups which play a role similar to free NO in inhibiting fibrinogen adsorption and preventing platelet aggregation; and 5) a preferred plasma coating in thickness of 20 nm which shows robust adhesion to SS substrates and no coating cracks observed after
  • the plasma treatment is for less than about five minutes, preferably for less than about two minutes, more preferably for less than about one minute, and most preferably for between about thirty seconds and about one minute.
  • the nitrogen-containing molecules are NH 3 and the oxygen-containing molecules are O 2 .
  • the mass flow rate during plasma treatment with each of NH 3 and of O 2 is between a ratio of about 1.5:1 and about 1:1.5.
  • the nitrogen-containing molecules are N 2 O and the oxygen-containing molecules are O 2 .
  • the mass flow rate during plasma treatment with each of N 2 O and of O 2 is between a ratio of about 1.5:1 and about 1:1.5.
  • the medical devices of this invention include stents, catheters, balloons, shunts, valves, pacemakers, pulse generators, cardiac defibrillators, spinal stimulators, brain stimulators, sacral nerve stimulators, leads, inducers, sensors, seeds, screws, anchors, plates and joints.
  • the at least one contacting surface may be a metallic material, or may be a polymeric material. If it is a polymeric material, it may be biodegradable.
  • the device can further include a biologically compatible coating deposited over the two-step plasma coating process.
  • the biologically compatible coating is a membrane formed from the plasma polymerization of hydrocyclosiloxane monomers.
  • the biologically compatible coating may be a polymer or co-polymer, such as poly acrylate, poly bisphenol A carbonate, polybutadiene, polycarbonate, poly butylene terephthalate, poly butryl methacrylate, polydimethyl siloxane, polyester, polyethyleneimine, poly methyl methacrylate, polypropylene, polystyrene, polysulfone, polyurethane, poly vinyl, poly vinyl acetate polylactide, polyglycolide, polycaprolactone, or polyvinylidine fluoride.
  • the invention further consists of a coating for an implantable medical device with at least one contacting surface for contacting a bodily fluid or tissue, which coating includes a first layer on the contacting surface that includes the product of the two step plasma coating process.
  • the coating may further include a second layer deposited over the first layer, which second layer includes the product of plasma polymerization of hydrocyclosiloxane monomers.
  • FIG. 1 Water contact angle of plasma coated stainless steel (SS) wafers using direct current (DC) and radio-frequency (RF) plasmas vs. aging time.
  • contact angle 77° ⁇ 3° (not shown in the Figure).
  • EC endothelial cells
  • SMC smooth muscle cells
  • FIG. 5 I/M (intimal area over media area) ratio of stented segments of porcine coronary arteries after 21 days stent implantation. Bare metal stent (BMS) was used as control. See FIG. 1 caption for notes to sample ID.
  • BMS Bare metal stent
  • the invention provides an implantable medical device with a plasma-modified surface, which medical device has at least one contacting surface for contacting a bodily fluid or tissue, wherein the contacting surface is modified by deposition of a thin layer of plasma coating and a subsequent plasma surface modification with nitrogen-containing molecules and oxygen-containing molecules.
  • the plasma-modified contacting surface exhibits significantly enhanced adhesion of endothelial cells, compared to a similar surface that is not plasma modified with the method provided in this invention, suggesting rapid endothelialization on plasma-modified implantable medical devices.
  • the invention comprises a structural component having at least one plasma-modified contacting surface with resultant desirable or medically-useful properties.
  • Suitable structural components with a contacting surface include medical devices that are intended to contact blood or other tissues, such as stents, catheters, shunts, grafts, and other medical devices known in the art.
  • the structural component may include a mesh, coil, wire, inflatable balloon, or any other device or structure which is capable of being implanted at a target location, including intravascular target locations, intraluminal target locations, target locations within solid tissue, such as for the treatment of tumors, and the like.
  • the implantable device can be intended for permanent or temporary implantation. Such devices may be delivered by or incorporated into intravascular and other medical catheters. Suitable surfaces include stainless steel, nitinol, titanium, other metal alloys, polyvinyl chloride, polyethylene, polylactide, poly glycolide, poly caprolactone, poly methyl methacrylate, poly hydroxylethyl methacrylate, polyurethane, polystyrene, polycarbonate, dacron, extended poly tetrafluoroethylene (Teflon®), related fluoropolymer composites (Gore-Tex®), or combinations thereof. All or part of the available surface can be modified.
  • substrate materials can also be used, including poly acrylate, poly bisphenol A carbonate, polybutadiene, poly butylene terephthalate, poly butryl methacrylate, polydimethyl siloxane, polyester, polyethyleneimine, polysulfone, poly vinyl acetate, polyvinylidine fluoride, polylactide, poly glycolide, poly caprolactone and copolymers and variants thereof.
  • a suitable method of exposing the structural components with a surface to the plasma involves placement of the structural components in a plasma field singly, in groups, or by methods involving fluidized bed or the like, which is disclosed in U.S. Pat. No. 6,613,432, and hereby incorporated by reference.
  • the present invention provides a nano-scale (less than 100 nm) plasma coating that is fabricated by a glow discharge plasma deposition process for an implantable medical device made of metals or alloys or polymers with at least one contacting surface for contacting a bodily fluid or tissue, and followed by plasma surface modification using a mixture of oxygen-containing molecules and nitrogen-containing molecules to create bioactive functional groups such as nitric oxide or oxynitrites on the surface.
  • This two-step plasma process is performed using two different plasma sources including radio-frequency (RF) and direct current (DC) without taking the wafers or stents out of plasma reactor between the two steps.
  • Silicon-containing monomers are used for thin coating deposition.
  • This type of organosilanes can be polymerized and deposited rapidly onto the substrate surface with good adhesion through a glow discharge plasma coating process.
  • the organosilanes usable for this purpose include trimethylsilane (TMS), vinyltrichlorosilane, tetraethoxysilane, vinyltriethoxysilane, hexamethyldisilazane, tetramethylsilane, vinyldimethylethoxysilane, vinyltrimethoxysilane, tetravinylsilane, vinyltriacetoxysilane, and methyltrimethoxysilane.
  • TMS trimethylsilane
  • vinyltrichlorosilane tetraethoxysilane
  • vinyltriethoxysilane hexamethyldisilazane
  • tetramethylsilane vinyldimethylethoxysilane
  • vinyltrimethoxysilane vinyltrimethoxysilane
  • vinyltriacetoxysilane vinyltriacetoxysilane
  • methyltrimethoxysilane methyltrimethoxysilane.
  • the silicon-containing monomers comprise a member selected from the organosilanes that can be vaporized at a temperature of less than 100° C.
  • the silicon-containing monomers comprise a member selected from the silane group consisting of (CH 3 ) 3 —SiH and (CH 3 ) 2 —SiH 2 .
  • the silicon-containing monomers comprise trimethylsilane (TMS). Plasma deposited organosilicon coatings exhibit not only as dense a film as conventional plasma coatings do, but also provides a certain degree of abrasion-resistance for the stent surface due to its inorganic —Si—Si— and —Si—C—Si— backbone.
  • the good adhesion is attributed to the formation of a chemical bond between the plasma-deposited layer and the surface of metals or polymers.
  • the resulting nano-scale (less than 100 nm) plasma coating is treated by a second plasma treatment using a mixture of nitrogen and oxygen molecules.
  • a mixture of NH 3 /O 2 is used for plasma surface treatment because these gases will be activated by the highly energetic electrons produced in the plasma chamber to form nitric oxide on the surface thereby providing long-lasting bioactivity to the surface which promotes endothelialization on the medical device surface, for example, stent struts.
  • the second steps of plasma treatment using a NH 3 /O 2 gas mixture provides the desired oxynitrite functional groups with a maximized amount attached onto the plasma coating surface, also through covalent bonding.
  • the combination of the two-step processed plasma coatings of the present invention provides a stable and durable functionalized surface and consequently results in significantly improved performance of the plasma coated implantable devices.
  • the functional and durable plasma coatings provided in this invention with two-step processes prove very cost-effective by creating bioactive agents on stent surfaces that inhibit both restenosis and in-stent thrombosis without using any drugs or reagents.
  • Non-drug-based stent coatings are considered a novel approach to improve the safety and efficacy of stents [Wessely et al. Nat Rev Cardiol, 7(4):194-203, 2010].
  • the structural components as used herein refer to virtually any device that can be temporarily or permanently implanted into or on a human or animal host.
  • Suitable structural components with a surface include those that are intended to contact blood including stents, catheters, shunts, grafts, and the like.
  • Suitable devices that are intended as tissue implanted include brachytherapy sources, embolization materials, tumor-bed implants, intra-joint implants, materials to minimize adhesions, and the like.
  • the device may include a mesh, coil, wire, inflatable balloon, bead, sheet, or any other structure which is capable of being implanted at a target location, including intravascular target locations, intraluminal target locations, target locations within solid tissue, typically for the treatment of tumors, and the like.
  • the implantable device can be intended for permanent or temporary implantation. Such devices may be delivered by or incorporated into intravascular and other medical catheters.
  • the device can be implanted for a variety of purposes, including tumor treatment, treatment or prophylaxis of cardiovascular disease, the treatment of inflammation, reduction of adhesions, and the like.
  • the device is used for treatment of hyperplasia in blood vessels which have been treated by conventional recanalization techniques, particularly intravascular recanalization techniques, such as angioplasty, atherectomy, and the like.
  • Exemplary structural components and devices include intravascular stents.
  • Intravascular stents include both balloon-expandable stents and self-expanding stents.
  • Balloon-expandable stents are available from a number of commercial suppliers, including from Cordis under the Palmaz-Schatz tradename.
  • Self-expanding stents are typically composed from a shape memory alloy and are available from suppliers, such as Instent.
  • a balloon-expandable stent is typically composed of a stainless steel framework or, in the case of self-expanding stents, from nickel/titanium alloy. Both such structural frameworks are suitable for use in this invention.
  • Exemplary devices also include balloons, such as the balloon on balloon catheters.
  • the construction of intravascular balloon catheters is well known and amply described in the patent and medical literature.
  • the inflatable balloon may be a non-dispensable balloon, typically being composed of polyethyleneterephthalate, or may be an elastic balloon, typically being composed of latex or silicone rubber. Both these structural materials are suitable for coating according to the methods of this invention.
  • the implantable devices will have one or more surfaces or a portion of a surface that is treated with gas plasma composed of molecular species containing oxygen and nitrogen.
  • gas plasma composed of molecular species containing oxygen and nitrogen.
  • stents it is particularly desirable to treat the entire surface.
  • balloons mounted on catheters it is desirable to coat at least the outer cylindrical surface of the balloon that will be in contact with the blood vessel when the balloon is inflated therein.
  • implantable structures such as wires, coils, sheets, pellets, particles, and nanoparticles, and the like, may be treated with the gas plasma containing molecular species composed of oxygen and nitrogen according to the methods of the present invention.
  • a stent delivery catheter typically an intravascular balloon catheter in the case of balloon-expanded stents or a containment catheter in the case of self-expanding stents.
  • the invention is thought to be particularly useful as applied to cardiovascular stents and for the prevention of restenosis following stent placement, and other interventional treatments, but may also be used in other therapies, such as tumor treatment or in controlling inflammation or thrombosis.
  • Any device in accord with the invention would typically be packaged in a conventional medical device package, such as a box, pouch, tray, tube, or the like.
  • the instructions for use may be printed on a separate sheet of paper, or may be partly or entirely printed on the device package.
  • the implantable device within the package may optionally be sterilized.
  • Stainless steel coronary artery stents when unexpanded had dimensions of 1.6 mm (diameter) ⁇ 12 mm (length) with a total exposed wire surface area of 20.66 mm 2 .
  • the stents were cleaned with a 2% (v/v) Detergent 8 solution for 30 min at 50° C. in an ultrasonic bath.
  • the stents were then sonicated in distilled water for 30 min at 50° C.
  • Stents were given a final rinse with distilled water and dried in an oven at 50° C. for 30 min.
  • the stents were then threaded through an electrically conductive metal wire that had been attached to aluminum panels with a surface area 15.3 cm ⁇ 7.6 cm, using silver epoxy.
  • DC treatment groups we used an oxygen pretreatment step (1 sccm oxygen, 50 mTorr, 20 W DC, 2 min) followed by TMS plasma polymer deposition (1 sccm TMS, 50 mTorr, 5 W DC, 15 s) and a 2:1 ammonia/oxygen plasma surface modification treatment for 2 min at 50 mTorr and 5 W DC.
  • RF treatment groups we used an oxygen pretreatment step (1 sccm oxygen, 50 mTorr, 20 W RF, 2 min) followed by TMS plasma polymer deposition (1 sccm TMS, 50 mTorr, 30 W RF, 4 min) and a 2:1 ammonia/oxygen plasma surface modification for 2 min at 50 mTorr and 5 W RF.
  • a cross-hatch was made using a razor blade on plasma coated stainless steel wafers followed by a Scotch® tape pull test. Visual inspection showed that there was no coating coming off the cross-hatched or its surrounding area, indicative of strong adhesion to the underlying surface, which warrants the coating integrity when flexed during stent crimping, navigation and expansion in clinical application.
  • Stainless steel stents of generic design in the dimension of ⁇ 1.6 mm ⁇ 12 mm (diameter ⁇ length) before dilation were used for the coating cracking test.
  • the stents were imaged using an optical microscope at 20 ⁇ and 50 ⁇ magnifications.
  • the samples were expanded with a balloon catheter (monorailTM Maverick PTCA Dilatation Catheter, Boston Scientific, Natick Mass.) and inflated to 3.0 mm in diameter; the stents were then visualized again via optical microscopy and Scanning Electron Microscopy (SEM) to determine if the expansion created any cracks on the plasma coatings.
  • SEM Scanning Electron Microscopy
  • NO functionalities can be durably maintained since they are covalently bonded to the plasma coated surface. It has been reported in the literature [Maalej et al. J Am Coll Cardiol. 33 (5): 1408-1414, 1999] that NO-coated surfaces are more resistant to binding of thrombogenic molecules such as fibrinogen. Fibrinogen and other serum proteins will bind to damaged endothelial surfaces or stent surfaces before platelet and mediate platelet adhesion and aggregation. Our previous studies also indicated that the nitrosated SS surface using NH 3 /O 2 plasma surface modification (no plasma coating deposition prior to NH 3 /O 2 plasma treatment) had an inhibitory effect on the binding of fibrinogen [Chen et al.
  • Endothelial recovery is an essential component for vascular healing by providing critical structural and anti-thrombogenic functions [Chin-Quee et al. Biomaterials, 31(4): 648-657, 2010].
  • Porcine coronary artery endothelial cells (EC), manufactured by Genlantis (San Diego, Calif.), were used for the evaluation of endothelialization.
  • the culture test was first performed on SS wafers at one week after plasma coating following a standard protocol. The results shown in FIG. 2 indicate that there were no cells observed on SS wafers coated with TMS alone in both DC and RF cases.
  • the TMS coating followed by NH 3 /O 2 plasma surface modification with DC and RF resulted in a 2.2 to 2.5 fold increase in endothelial cell adhesion/growth after 3 days of culture as compared to bare SS.
  • VSMC Vascular Smooth Cell
  • Stainless steel wafers with and without plasma coatings or treatment were sterilized by UV light for 2 hours on each side, then placed in a 24 well plate using 2 wafers from each of the 5 groups.
  • 50,000 human coronary artery VSMCs (Catalog Number: C-017-5C, Invitrogen, Carlsbad, Calif.) were then seeded into each well containing one wafer and let grow for 1 day. Then those wafers with cells were fixed in 3% gluteraldehyde, and stained with toludine blue, and rinsed. After rinsing to remove unbound stain, the wafers were then examined by epifluorescence and digitally photographed. The number of cells on each micrograph field was then counted.
  • FIG. 4 indicates that the plasma coated wafers with DC-NH 3 /O 2 or RF-NH 3 /O 2 resulted in lower smooth muscle cell attachment than bare stainless steel wafers
  • Neointimal (NI) area was calculated (vessel area-lumen area-medial area). The ratio of intimal area over media area (I/M) of stented segments was shown in FIG. 5 .
  • the DC-NH 3 /O 2 coated stent (TMS coating followed by NH 3 /O 2 plasma surface modification with DC plasma) is significantly better than the BMS control in suppressing coronary restenosis (p ⁇ 0.001 in paired t-Test based on 3 stent sections of one stent), suggesting its great promise of inhibiting smooth muscle proliferation and thus limiting in-stent restenosis.
  • this invention provides a very different approach to solve the biocompatibility problems with stents by offering great potential to reduce the risk of restenosis and inhibit late stent thrombosis simultaneously.
  • our unique two-step plasma coating approach features in: 1) the 1st step of the plasma deposition process, using a silicon-containing monomer creates a uniform and conformal nano-scale plasma coating that not only has tenacious adhesion through the strongest covalent bonding to stent surfaces but also provides a coating surface chemistry being suitable for new functional groups to attach; 2) the 2nd step of plasma treatment using an NH 3 /O 2 gas mixture will create the desired oxynitrite functional groups with a maximized amount attached onto the plasma coating surface, also through covalent bonding; and 3) combination of the two-steps will thus provide a stable and durable functionalized surface and consequently result in significantly improved performance of the plasma coated coronary stents. As demonstrated in the embodiments, this two-step plasma coating approach has shown great promise in improving the long term biocompatibility of

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EP2744852A4 (fr) 2015-04-15
US20170296708A1 (en) 2017-10-19
EP2744852B1 (fr) 2017-12-20
JP2014521486A (ja) 2014-08-28
US20160184489A1 (en) 2016-06-30
US9603978B2 (en) 2017-03-28
WO2013025317A1 (fr) 2013-02-21
US10016533B2 (en) 2018-07-10
JP6132106B2 (ja) 2017-05-24
CN103748147B (zh) 2016-07-06
ES2663099T3 (es) 2018-04-11
CN103748147A (zh) 2014-04-23

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