METHOD FOR COATING A MEDICAL DEVICE AND MEDICAL DEVICE

专利摘要:
coatings and methods of coating surgical needles. The present invention features innovative medical devices for use in surgical procedures and methods for manufacturing medical devices. in some modalities, innovative medical devices may include surgical needles that are capable of being repeatedly passed through tissue with the use of minimal force. more particularly, surgical needles can be manufactured with one or more coatings that provide durability and lubricity to the surgical needles to facilitate successive and repeated passages through tissue. innovative methods of manufacturing surgical needles and supplying and applying coatings to surgical needles are also provided.
公开号:BR112012010995B1
申请号:R112012010995-2
申请日:2010-10-21
公开日:2021-08-17
发明作者:Robert Maurer；S. Neil Bar；Eric Hinrichs；Michael Hamilton；Thomas Wilkes
申请人:Ethicon Llc；
IPC主号:

专利说明:

CROSS REFERENCE TO RELATED ORDERS
[001] This application is a continuation-in-part of US Patent Application Serial No. 12/614,669, filed November 9, 2009 entitled "Surgical Needle Coatings and Methods", and US Patent Application No. series 12/614,665 filed November 9, 2009 entitled "Surgical Needle Coatings And Methods" which are incorporated herein by reference in their complete form. FIELD OF THE INVENTION
[002] The present invention relates to coated medical devices and methods for manufacturing them. BACKGROUND OF THE INVENTION
[003] Coated medical devices that repeatedly contact body tissue, such as surgical needles, need to be slippery but durable enough to withstand multiple tissue contacts. However, lubricity is often sacrificed at the expense of producing a more durable coating that adheres well to medical devices. There are many coating materials that are extremely slippery but do not adhere well to the desired substrates, or easily wear onto the substrate during use. Similarly, many extremely durable coatings exist, but these coatings are not considered slippery. Several attempts have been made to find coating compositions and/or a method of applying coating compositions that can provide durability and lubricity simultaneously. Consequently, the present invention addresses this issue by providing coating compositions and application methods, which provide both durability and lubricity, as well as shorter manufacturing time. SUMMARY OF THE INVENTION
[004] The present invention provides methods and devices for providing a durable and slippery medical device, structure and/or body. In an exemplary embodiment, a method for coating a body, structure and/or medical device is provided and may include providing a medical device and applying a single, homogeneous coating to at least a portion of a surface of the device. with a thickness in the range of about 1 micron to about 12 microns. While the single, homogeneous coating may have many components, in some embodiments, the single, homogeneous coating may include a vinyl-functionalized organopolysiloxane and a polydimethylsiloxane. Applying a single homogeneous coating to a surface of the medical device can include applying a coating having a thickness in the range of from about 1 micron to about 3.5 microns. In one embodiment, the surface of the medical device can include a primer that includes a silicone. The single homogeneous coating can be sprayed onto a surface of the medical device. The surface can be an exterior surface, an interior surface, or a combination of interior and exterior surfaces. In some embodiments, the homogeneous coating can be cured on the surface of the medical device for a period of time in the range of about 10 seconds to about 30 seconds.
[005] The medical device can be formed from any suitable material known in the art including tungsten alloys, refractory alloys, stainless steels, nitinol and tantalum. The tungsten alloy can be, for example, tungsten-rhenium. In some embodiments, application of a single homogeneous coating may include delivering the single homogeneous coating to the surface of the medical device in a solvent of low boiling point and high vapor pressure. The low boiling high vapor pressure solvent can be, for example, a hydrofluorinated ether solvent. The single, homogeneous coating can be applied to any medical device known in the art, and in some embodiments, the method can include providing an elongated medical device that has a tissue penetrating portion.
[006] In other aspects, devices are provided, and in an exemplary embodiment, a coated device is provided and may include a substrate, wherein at least a portion of the substrate is coated with a coating comprising a vinyl-functionalized organopolysiloxane and a polydimethylsiloxane. The coating can be a single layer having a thickness in the range of from about 1 micron to about 3.5 microns. In some embodiments, the coating can be configured to be delivered to the substrate in a low boiling, high vapor pressure solvent such that the body exhibits substantially constant penetration over thirty body passes through the tissue. The device can be formed from any suitable material known in the art including tungsten alloys, refractory alloys, stainless steels, nitinol and tantalum. In some embodiments, the substrate can be a medical device. In addition, the coating includes vinyl-functionalized organopolysiloxane in the range of about 10% by weight to about 90% by weight and polydimethylsiloxane in the range of about 10% by weight to about 90% by weight. The vinyl-functionalized organopolysiloxane can be, for example, Momentive® silicone product code MSC2631, product no. produced by Momentive® Performance Materials of Waterford, NY, USA.
[007] In another aspect, a medical device is provided and may include a structure and/or body and a single, homogeneous coating comprising a slippery silicone disposed on a surface, for example, an exterior and/or interior surface of the body. The body can exhibit substantially constant penetration over thirty passes of the substrate through the tissue. In some embodiments, the single, homogeneous coating can be formed of a vinyl-functionalized organopolysiloxane and a polydimethylsiloxane. The body can have many configurations known in the art, and can include an elongated body having a tissue penetrating portion. Furthermore, the medical device may be an assembly that includes a plurality of components and/or operating parts, and the body may be one of the plurality of components and/or operating parts. One or more, and in some cases the entirety of the plurality of components and/or operating parts can be coated with the single, homogeneous coating.
[008] In some embodiments, the single, homogeneous coating can be configured to be cured at a temperature of about 200 degrees Celsius using infrared radiation with a wavelength in a range from about 1.4 µm to about 3, 0 µm. The single, homogeneous coating can also be configured to cure for a period of time in the range of about 1 second to about 60 seconds and/or for a period of time in the range of about 10 seconds to about 30 seconds. In other embodiments, the single, homogeneous coating can be configured to be cured on the body surface in a convection oven for a period of time in the range of about 1 hour to about 5 hours at a temperature of about 60 degrees Celsius at about 180 degrees Celsius and/or for a period of time in the range of about 2.5 hours to about 3.5 hours at a temperature of about 100 degrees Celsius to about 140 degrees Celsius.
[009] In still other aspects, methods for coating a medical device are provided and may include providing a slippery silicone coating comprising a solvent having a boiling point less than about 43 degrees Celsius. The method can also include applying the slippery silicone coating to the medical device and curing the slippery silicone coating for a period of time in the range of about 1 second to about 60 seconds. The solvent can have a vapor pressure of, for example, about 350 mm Hg. Additionally, curing the slippery silicone coating may include curing the coating at a temperature of about 200 degrees Celsius for a period of time in the range of about 10 seconds to about 30 seconds using infrared radiation with a wavelength in the range from about 1.4 µm to about 3.0 µM. Although the slippery silicone coating can be formed from many compositions, in one embodiment the slippery silicone coating can include a single, homogeneous layer of a vinyl-functionalized organopolysiloxane and a polydimethylsiloxane.
[0010] The invention will be understood more fully from the following detailed description, taken in conjunction with the attached drawings, in which: BRIEF DESCRIPTION OF THE DRAWINGS
[0011] Figure 1 is a perspective view of an exemplary embodiment of a surgical needle;
[0012] Figure 2 is a side view of a carrier strip with surgical needles attached thereto for carrying the surgical needles;
[0013] Figure 3A is a perspective view of an exemplary embodiment of a swirl coating machine for swirl coated surgical needles;
[0014] Figure 3B is a perspective view of another exemplary embodiment of a swirl coating machine for coating suspended surgical needles;
[0015] Figure 4A is a flowchart of an exemplary method for manufacturing and coating surgical needles using two coatings;
[0016] Figure 4B is a flowchart of an exemplary method for manufacturing and coating surgical needles using a single, homogeneous coating;
[0017] Figure 5 is a graphical representation comparing the force required to pass primed and unprimed surgical needles through synthetic means;
[0018] Figure 6 is a graphical representation comparing the force required to pass surgical needles that are swirl coated through synthetic means versus surgical needles that are dip coated;
[0019] Figure 7 is a graphical representation comparing forces associated with two different coating compositions and application methods;
[0020] Figure 8 is a graphical representation comparing the force required to pass surgical needles that are swirl coated through synthetic means versus surgical needles that are dip coated;
[0021] Figure 9 is a graphical representation comparing the forces associated with the passage of three different coating compositions and application methods through human cadaver tissue; and
[0022] Figure 10 is a graphical representation comparing the forces associated with the passage of needles with a single, homogeneous coating and needles coated with two coatings through synthetic means. DETAILED DESCRIPTION
[0023] Certain exemplary embodiments will now be described to provide a general understanding of the principles of structure, function, fabrication, and use of the devices and methods described herein. One or more examples of three modalities are illustrated in the accompanying drawings. Those skilled in the art will understand that the devices and methods specifically described herein and illustrated in the accompanying drawings are non-limiting exemplary embodiments, and that the scope of the present invention is defined solely by the claims. Aspects illustrated or described in connection with one exemplary embodiment may be combined with aspects of other embodiments. These modifications and variations are intended to be included within the scope of the present invention.
[0024] The present invention presents, in general, innovative medical devices for use in surgical procedures and methods for manufacturing innovative medical devices. In some embodiments, innovative medical devices can include one or more bodies, one or more structures, and/or an array of components and/or operating parts. In one modality, innovative medical devices may include surgical needles that are capable of being repeatedly passed through tissue with easy penetration. More particularly, innovative surgical needles can be manufactured with two or more coatings that provide durability and lubricity to surgical needles to facilitate successive and repeated passes through tissue. Innovative methods of manufacturing surgical needles and providing and applying durable coatings to surgical needles are also provided. As used herein, the terms "coating" and "coating" are used interchangeably.
[0025] Although many types of medical devices and surgical needles are contemplated, in one modality, a biocompatible surgical needle is provided that has a single, homogeneous coating applied to it so that the coating is both durable and slippery. The single, homogeneous coating can be applied to an exterior and/or interior surface of a medical device, and may be applied to one or more portions of the exterior and/or interior surfaces. The single, homogeneous coating can be a partial and/or discontinuous coating of the outer and/or inner surface, or it can be applied to the entire outer and/or inner surface. In another embodiment, two or more different coatings can be successively applied to the surgical needle. A base coat can be applied to the needle to provide durability for a different top coat that is applied to provide lubrication. The base coat can also be slippery to enhance the lubricity of the top coat. In some embodiments, the single, homogeneous coating may cross-link to itself and/or the base and top coatings may interact, for example, by cross-linking or by one or more other binding mechanisms. Due to the bond between the base coat and the top coat, the base coat holds the top coat over the surgical needle. In this way, the base coat can help prevent the top coat from fraying and/or corroding after repeated passes through the fabric. In other embodiments, each of the base coat and/or top coat may cross-link to itself. The interaction between components within the single, homogeneous coating and/or between the base coat and the slippery top coating aids in maintaining lubrication of the surgical needle so that it can consistently and repeatedly be passed through tissue with minimal force required.
[0026] Any number of coatings can be applied to the surgical needle depending on the surgical application and the composition of the surgical needle. For example, in another embodiment a primer coating can be applied to the surgical needle before the single, homogeneous coating and/or base and top coatings are applied. The primer coating may be different from the homogeneous single coating and/or the base and top coatings and may bond with a surgical needle surface to provide a suitable and secure surface on which to apply the base coat. In turn, the single, homogeneous coating and/or base coating may bond to the primer coating in such a way that the primer coating securely retains the single, homogeneous coating or base coating on the surgical needle.
[0027] Innovative methods for applying the coatings on various medical devices, such as surgical needles, are also presented. In some embodiments, a surgical needle can be spray coated with one or more coatings to provide the surgical needle with an even distribution thereof. For example, a spray coating machine that has two spray nozzles directed towards each other can be provided for applying the single, homogeneous coating or for successively applying each top or base coat. One or more surgical needles may be passed between the two spray nozzles as they spray a liner. Such a configuration allows for even distribution of the coating on the surgical needle and minimizes the risk of pooling and/or dripping of the coating. Multiple coatings can be applied using this method, and before and/or after applying each coating, the surgical needle can be cured for a period of time effective enough to adjust and bond the coating(s) . As will be discussed in greater detail below, innovative combinations of solvents and coating materials can allow for substantially reduced cure times compared to techniques known in the art.
[0028] Exemplary surgical needles of the type contemplated herein may generally be used for any surgical procedures not known or yet to be developed. Surgical needles can be able to penetrate and pass through any type of tissue, including any type of mammalian tissue including soft and hard tissue and tissue that has been calcified, and can be used to apply sutures to close an incision or wound, pass suture or other material through the tissue, and/or simply create an opening in the tissue. One of skill in the art will note the variety of uses for the surgical needles described herein.
[0029] Exemplary surgical needles may generally include an elongated member with a tissue penetrating tip at a distal end thereof to penetrate through tissue. The tissue-penetrating tip can be pointed and can be as sharp or as blunt as needed for a particular surgical procedure. In some embodiments, the surgical needle may also include a suture attachment portion disposed over a proximal end of the elongate suture receiving and retaining member. The surgical needle can have any geometry known in the art, including straight, tapered tip, tapered cut, cutting edge, bayonet-shaped, curved, circular, etc. In addition, the surgical needle may have any cross section including, but not limited to, round body, rectangular body, square body, ovular body, and I-beam. A person skilled in the art will note the various combinations of shapes and cross sections possible for a given needle.
[0030] In the manufacturing process, surgical needles may have a straight and/or hook-shaped gripping portion to aid in the application of coatings on them. A transport mechanism and/or carrier strip for manufacturing a needle and/or moving a needle through a coating machine and/or curing mechanism can retain the needle for fabrication, coating, and curing by attaching to the portion of seizure. An exemplary carrier strip 20 for use with surgical needles 24 is illustrated in Figure 2. Carrier strip 20 includes a plurality of latches 22 for retaining curved surgical needles 24 therein. This allows the surgical needles 24 to be moved using a carrier style mechanism during the coating and/or curing process.
[0031] An exemplary embodiment of a surgical needle is illustrated in Figure 1. As shown, a surgical needle 10 is provided that has an elongated curved body 16 with a tissue penetrating tip 12 formed at a distal end thereof. Tip 12 has a circular cross section and ends in a sharp point to penetrate tissue. The curved elongated body 16 extends between the tip 12 and a suture attachment portion (not shown) and is in the form of an arc with a flat rectangular cross section. Although surgical needle 10 may have any relative dimensions as needed, in the illustrated embodiment, a width W of needle 10 is on the order of a height H of needle 10. A suture attachment portion may have any shape necessary for receiving and suturing sutures. retention.
[0032] Exemplary surgical needles can be formed from any suitable biocompatible material known in the art. In some embodiments, a surgical needle can be produced from a metallic alloy, including, but not limited to, titanium, stainless steels such as 420 stainless steel, 455 stainless steel, ETHALLOY® needle alloy, and 302 stainless steel, alloys refractories, nitinol, tantalum, as well as various other materials and alloys known in the art. In other modalities, surgical needles can be made from a tungsten-rhenium alloy. The use of tungsten-rhenium alloy in the production of surgical needles can yield the needles greater rigidity, strength, and ductility than the use of some other materials. The enhanced hardness and strength properties allow the needle to be resistant to elastic deformation and thus resist bending and compression deformation when pushed through hard tissue, eg calcified tissue. The heightened ductility prevents the needle from breaking when bent or bent by a surgeon. Any of the needle alloy compositions may contain some percentage of any one or more of nickel, cobalt, chromium, molybdenum, tungsten, rhenium, niobium, etc. Exemplary needles and methods for manufacturing needles and carrier strips can be found in US Patent No. 6,018,860 entitled "Process for Manufacturing Drilled Taper Point Surgical Needles", which is incorporated herein by reference in its entirety. .
[0033] In some embodiments, two or more different coatings can be used to provide exemplary surgical needles with a durable, slippery surface for repeated passes through tissue. In an exemplary embodiment, a base coat can be used to coat an outer surface of a surgical needle to provide durability to a top coat that is applied over the base coat and provides lubrication. The basecoat preferably bonds to the topcoat and thereby prevents and/or lessens wear associated with repeated penetrations and passages through the fabric. In some embodiments, a primer coat can optionally be applied before the base coat. The primer coat can bond with the surface of the surgical needle to provide a bonding surface for the base coat. Primer coating can add additional wear and tear to the base coat and top coat.
[0034] The basecoat may include, for example, a silicone-based composition characterized as a vinyl-functionalized organopolysiloxane. The basecoat solution includes a vinyl-functionalized organopolysiloxane, fluid polymethylhydrogen siloxane crosslinking agent, and optionally a catalyst such as a conventional metal catalyst such as platinum or tin. The basic organopolysiloxane polymer can be, for example, Momentive® silicone product code MSC2631 from product no. produced by Momentive® Performance Materials of Waterford, NY, USA. More information on the MSC2631 composition is available from the manufacturer's MSDS.
[0035] The basecoat can be prepared using any low boiling, high vapor pressure solvent known in the art. In some embodiments the solvent may be a hydrofluorether ("HFE") (for example, HFE 72-DE solvent produced by 3M® of St. Paul, MN, USA). The HFE solvent acts as a carrier for the silicone composition. It quickly evaporates from a composition under ambient conditions to limit the migration of other substances into the composition and thus drastically reduces the curing time of the composition. Furthermore, the HFE solvent does not leave residues after evaporation. It complies with health and safety regulations and is environmentally friendly. As will be understood by those of skill in the art, any suitable solvent can be used including, but not limited to, HFE, xylene, heptane, IsoPar K (Dow Corning), naphthalene, toluene, and hydrofluorocarbons.
[0036] Additionally, a catalyst and a crosslinker can be added to the basecoat. For example, the Momentive® platinum catalyst, product code no. SS8010 ("catalyst") and the Momentive® crosslinker product code no. SS4300 ("crosslinker"), both produced by Momentive® Performance Materials of Waterford, NY, USA, can be added during basecoat preparation to act as a crosslinker and catalyst. As will be understood by those skilled in the art, any suitable catalysts and crosslinkers can be used including, but not limited to, other crosslinkers that contain a chemical moiety of silicon hydrogen. Other catalysts can include conventional metallic catalysts such as tin.
[0037] In preparing an exemplary basecoat, 27.57% by weight of the base silicone polymer, for example a vinyl-functionalized organopolysiloxane, may be combined with 72.27% by weight of the HFE solvent and mixed and/ or stirred for a suitable period of time, for example for about five minutes. The catalyst may then be added to the mixture at 0.02% by weight and the crosslinker may be added at 0.14% by weight. The mixture can be stirred for a few more minutes to ensure homogeneity, for example about one to two more minutes. For an exemplary 48.43 g basecoat sample, 13.35 g of the silicone polymer base may be combined with 35.00 g of the HFE solvent, 0.012 g of the catalyst, and 0.068 g of the crosslinker.
[0038] A topcoat can be applied on a surgical needle. In some embodiments, the topcoat can include a silicone-based composition characterized as a hydroxyl-terminated polydimethyl siloxane. The hydroxyl-terminated polydimethyl siloxane generally includes dimethyl-terminated hydroxy siloxane, methyl hydrogen siloxane, and trace amounts of various other siloxanes. The hydroxyl terminated polydimethyl siloxane can be, for example, NuSil® Technologies Silicone, Product No. MED4162 produced by NuSil® Technologies of Carpentaria, CA, which is a dispersion that contains 30% silicone solids in a 70% carbon. xylene solvent reactor.
[0039] The topcoat can be prepared with the use of a solvent, eg HFE solvent or any other compatible volatile solvent. When preparing an exemplary topcoat, 26% by weight of the silicone polymer topcoat can be combined with 74% by weight of the HFE solvent. For example, for a 50 g topcoat sample, 13.00 g of the top silicone polymer can be combined with 37.00 g of the HFE solvent.
[0040] In some embodiments, a primer coat may optionally be applied to a surgical device prior to application of the base coat. The primer coat can be any formulation capable of binding to a surgical needle and capable of providing a suitable substrate for applying a base coat. In one embodiment, the primer coating can be formed from, for example, polyalkyl siloxane and tetraethyl silicate. A polyalkyl siloxane and tetraethyl silicate coating primer can be formulated to coat difficult bond substrates such as tungsten-rhenium alloys.
[0041] An example of a primer coating of polyalkylsiloxane and tetraethyl silicate is Momentive®, Product No. SS4044P ("primer SS4044P") produced by Momentive® Performance Materials of Waterford, NY, USA. Primer SS4044P may include Momentive®) 10 to 30% by weight of acetone, 1 to 5% by weight of butanol, 10 to 30% by weight of mixture of xylene isomers, 5 to 10% by weight of ethylbenzene , 10 to 30% by weight of 2-propanol, 1 to 5% by weight of tetraethyl silicate, and 10 to 30% by weight of polyalkyl siloxane. Additional information on SS4044P primer composition is available from the manufacturer's MSDS.
[0042] In general, as noted above, the primer coating can covalently bond to the surgical needle to provide a substrate to which other coatings are applied. The base coat can be applied on top of the primer coat. As the top coat is applied over the base coat, the base coat will bond to the top coat to provide durability to the top coat. In essence, the bond between the primer coating and the surgical needle anchors the other two coatings to the surface of the needle. Bonding the base coat to both the primer coat and the top coat anchors the top coat to the primer coat, and thereby to the surface of the surgical needle, providing extended durability to the top coat.
[0043] Coatings can generally be applied in any thickness as required. The thickness of the individual coatings and the combined coatings must be sufficient to effectively provide the desired characteristics. For example, the primer coating can be applied to have a thickness in the range of about 0.01 µm to about 1 µm. Basecoat and topcoat can be applied with a thickness in the range of about 1 µm to about 7 µm. In an exemplary embodiment, the topcoat can have a thickness that is at least about 50% less than a thickness of the basecoat. One of skill in the art will understand that coating thicknesses can vary depending on a particular application.
[0044] In another modality, a medical device such as a surgical needle may be coated with a single, homogeneous, durable and slippery coating, composed, usually of a combination of a vinyl-functionalized organopolysiloxane, eg, Momentive® product code No. MSC2631 silicone manufactured by Momentive® Performance Materials of Waterford, NY, and a hydroxyl terminated polydimethylsiloxane, e.g., NuSil® Technologies Silicone Product No. MED4162 manufactured by NuSil® Technologies of Carpentaria, CA, which may also include a crosslinker or catalyst . The single, homogeneous coating can be a homogeneous mixture of the vinyl-functionalized organopolysiloxane and the hydroxyl-terminated polydimethylsiloxane so that when it is applied to a surface of a surgical needle, there is a single homogeneous layer formed on it. For example, in some embodiments, the single, homogeneous coating may be a mixture of the top and base coats mentioned above. In other embodiments, it can be any combination of the durable and slippery materials mentioned herein. The single, homogeneous coating can be applied to the medical device in a single application step, and in some embodiments, the single, homogeneous coating can be formed from various ratios of the top and base coatings described above. The single, homogeneous coating can be applied directly to the surface of a medical device and can be the only coating applied to the medical device so that there is a single coating layer formed on the surface of the medical device.
[0045] In preparing a single and homogeneous exemplary coating composition, the vinyl functionalized organopolysiloxane and the hydroxyl terminated polydimethylsiloxane can be prepared in various amounts, optionally with a catalyst and a crosslinking agent in a high viscosity solvent. In general, the vinyl-functionalized organopolysiloxane can be added to the composition in a range of about 2% by weight to about 25% by weight, and more preferably in a range of about 9% by weight to about 19%. by weight. Likewise, the hydroxyl terminated polydimethyl siloxane can be added to the composition in a range of about 2% by weight to about 25% by weight and more preferably in a range of about 9% by weight to about 19% by weight. Weight. A high vapor pressure, low boiling point solvent such as the HFE solvent can be added to the composition in a range of from about 65% by weight to about 85% by weight, and more preferably in a range of about from 70% by weight to about 80% by weight. In some embodiments, a catalyst and a crosslinker can be added to the composition. For example, a catalyst such as Momentive® platinum catalyst, product code no. SS8010, can be added in a range of about 0.002% by weight to about 0.070% by weight, and more preferably in a range of about 0.008 % by weight to about 0.05% by weight. A crosslinker such as Momentive® crosslinker product code no. SS4300, can be added in the range of about 0.01% by weight to about 0.40%, and more preferably in the range of about 0.04% by weight to about 0.28% by weight.
[0046] Alternatively, the single and homogeneous coating composition can be prepared by combining the basecoat and the topcoat (both described above) for various reasons. Separate batches of each coating can be produced and various amounts of coating can be combined. For example, the base coat to top coat ratio can be in the range of about 1:5 to 5:1, and more preferably in the range of about 1:3 to 3:1, for example, about 1:2, 1:1, 2:1, 1:3, 3:1, etc. As will be appreciated by those of ordinary skill in the art, any ratio combination of top and base coats may be used, including fractional ratios such as about 0.5:1, 1:0.5, 1:1.5, 1.5:1, 1:2.5, 2.5:1, etc.
[0047] In some embodiments, the single, homogeneous coating can be formed from a mixture of about 18.38% by weight of the silicone base polymer, eg, vinyl-functionalized organopolysiloxane, combined with about 72.85% by weight of the HFE solvent. The silicone base polymer and HFE solvent can be combined with about 8.667% by weight of the silicone polymer, for example, the hydroxyl terminated polydimethylsiloxane. Momentive® SS8010 platinum catalyst can be added to the mixture in a suitable amount (eg about 0.0165% by weight) and Momentive® SS4300 crosslinker can be added in a suitable amount (eg about 0, 0936% by weight). The mixture can be stirred for a few minutes to ensure homogeneity, for example about one to two more minutes. This mixture is equivalent, for example, to a ratio of about 2:1 (by weight) of the base and top coats.
[0048] In another embodiment, the unique and homogeneous exemplary coating can be formed from a mixture of about 13.78% by weight of the silicone base polymer, e.g., vinyl-functionalized organopolysiloxane, combined with about of 73.13% by weight of the HFE solvent. The silicone base polymer and HFE solvent can be combined with about 13.00% by weight of the silicone polymer, for example, the hydroxyl terminated polydimethylsiloxane. The catalyst can then be added to the mixture at about 0.0124% by weight and the crosslinker can be added at about 0.0702% by weight. This mixture is equivalent, for example, to a ratio of about 1:1 (by weight) of the base and topcoat solutions.
[0049] In yet another embodiment, the unique and homogeneous exemplary coating can be formed from a mixture of about 9.189% by weight of the silicone base polymer, for example, the vinyl-functionalized organopolysiloxane, combined with about 73 .42% by weight of the HFE solvent. The silicone base polymer and HFE solvent can be combined with about 17.33% by weight of the silicone polymer, for example, the hydroxyl terminated polydimethylsiloxane. The catalyst can then be added to the mixture at about 0.083% by weight and the crosslinker can be added at about 0.0468% by weight. This mixture is equivalent, for example, to a ratio of about 1:2 (by weight) of the base and topcoat solutions.
[0050] As will be appreciated by those skilled in the art, there are several conventional methods of mixing base and top coating solutions using conventional processing equipment and techniques to achieve different weight ratios within the single, homogeneous coating. In a blending method, master batches of basecoat and topcoat can each be mixed. The appropriate ratios of each coating can then be mixed together from the master batches to form the single, homogeneous coating. For example, if single, homogeneous coating with about a 2:1 ratio mix of basecoat and topcoat is desired, then an amount of topcoat can be mixed with twice the amount of topcoat of base coat, for example, about 20 grams of the base coat mixed with about 10 grams of the top coat. Or, if a single, homogeneous coat with about a 1:1 ratio is desired, then equal parts of the base and top coat can be mixed. In another modality, the single homogeneous combined coating can be produced directly with all the components being added directly in their correct proportion, rather than mixing separate master batches of the top and base coatings.
[0051] In some embodiments, a primer coating can optionally be applied to a medical device prior to a single, homogeneous coating. As noted above, the primary coating can be any formulation capable of binding to a medical device and capable of providing a suitable substrate for application of the single, homogeneous coating. In one embodiment, the primer coating can be formed from, for example, polyalkyl siloxane and tetraethyl silicate. A polyalkyl siloxane and tetraethyl silicate primer coating can be formulated to coat difficult bond substrates such as tungsten-rhenium alloys. In other embodiments, a primer coating is not desired or required, and the single, homogeneous coating is applied directly to the substrate, ie, the surface of the medical device and is the only coating applied to the medical device. In still other embodiments, a surface of the medical device may include a primer coating as a part thereof and/or preformed thereon such that when the single, homogeneous coating is applied, there is only a single coating layer on the device. doctor.
[0052] The single, homogeneous coating can generally be applied in any thickness as required. The thickness of the single, homogeneous coating must be sufficient to effectively provide the desired characteristics. For example, the single, homogeneous coating can be applied with a thickness in the range of from about 1 µm to about 12 µM and more preferably from about 3 µm to about 6 µm or from about 1 µm to about 3 .5 µm. If the primer coating is applied, it can be applied to have a thickness in the range of about 0.01 µm to about 1 µm. A person skilled in the art will appreciate that the thickness of the single, homogeneous coating and/or primer coating may vary depending on a particular application.
There are many methods and systems contemplated herein that can be used to deliver coated surgical needles or other medical devices. In general, a medical device such as a surgical needle can be produced from a desired material and prepared for coating, as described in more detail below. One or more coatings can be applied to the surgical needle to provide durability and lubricity during use. Before, during, and/or after applying any of the coatings, the surgical needle can be cured for an amount of time effective enough to remove solvents in the coatings and/or to adjust, cross-link, and/or bond a coating.
[0054] Any process known in the art can be used to coat various medical devices with one or more of a basecoat, a topcoat, a single coat composed of a mixture of a basecoat and a topcoat (or two). basecoat and topcoat components) and/or a primer coat including, but not limited to, dipping, spraying, wiping, brushing, full dipping, gravity feed, etc. For example, surgical needles can be dip coated in a number of traditional ways. If needles are processed manually, the needles can be immersed by hand or completely submerged in a coating. In a more automated process, coating solutions can be applied using a dam-type circulation system in which surgical needles pass through the solution in an automated fashion, either by a robot or handling system. In general, dipping techniques rely on surface tension for coating adhesion and wetting characteristics of the coating relative to the substrate for continuity. A person skilled in the art will appreciate the various possible conventional processes, process equipment, and equivalents thereof, which can be used for the various techniques.
[0055] In one embodiment, one or more coatings can be applied to a surgical needle by spraying with the use of, for example, ultrasonic and/or gas conformal coating spray head systems and/or swirl coating systems . Ultrasonic and gas spray nozzles transmit energy to a liquid in an amount sufficient to atomize the liquid and form a spray of droplets. Droplet spray can be applied to a medical device using a swirl process in which droplets are spiraled around the medical device to coat the substrate. Applying a coating using the swirl process can ensure more even distribution of the coating on a surgical device while avoiding over-collection of the coating, which can result in dripping, puddle formation, droplets, and/or unwanted irregularities . Sprinkling also allows for precise control and adjustment of coating thickness. A particular coating can be applied to leave only a thin film on a surface or the same can be applied to give different thicknesses.
[0056] Different types and sizes of spray nozzles can be used, depending on the specific coating compositions and the desired attributes of the generated spray stream. Spray nozzles can be designed to operate at specific frequencies and/or air pressures as needed, and the desired power level for nozzle operation may depend on a number of factors including nozzle size and design, the viscosity of the nozzle. composition being used, the volatility of the components in the composition being used, etc. Both ultrasonic and fluid spray nozzles are commercially available.
[0057] In one embodiment, as illustrated in Figures 3A and 3B, opposing spray nozzles 30a, 30b are provided for applying a swirl coating to exemplary surgical needles 32. Opposite spray nozzles 30a, 30b may each be one, coupled to tubes which retain a particular coating to be applied and can release the coating through discharge openings 31a, 31b. Each coating to be applied via the swirl process can be applied using different pairs of opposing spray nozzles 30a, 30b. Thus, in some embodiments, multiple sets of spray nozzles can be used to apply multiple coatings. Each spray head 30a, 30b can have a splined tip (not shown) to release the coating. An angle of the fluted tip, relative to the horizontal plane through which the needles extend perpendicularly, can be adjusted to focus the spray band to optimize coating. As will be understood in the art, any angle can be used as needed to release a particular coating. Also, different coatings may require releasing a fluted tip at a different angle.
[0058] The opposite pair of spray nozzles 30a, 30b may extend from a positioner (not shown) capable of adjusting and maneuvering the spray nozzles 30a, 30b in three dimensions. Opposite spray nozzles 30a, 30b can be positioned in any way relative to one another as needed for a particular application and can generally be symmetrically opposed to each other. In the illustrated embodiment, the spray nozzles 30a, 30b are positioned at approximately an angle of about 30 degrees, as shown in Figures 3A to 3B, with respect to a horizontal surface. Horizontally, the nozzles 30a, 30b can be directly opposite, for example offset by about 180 degrees. Preferably, however, the nozzles 30a, 30b may be offset horizontally relative to one another by an amount less than about 180 degrees to prevent neutralization and to prevent overspray from accumulating on the needles. The positioning of opposing nozzles 30a, 30b can be optimized to provide the most complete coating of a surgical needle.
[0059] In general, the swirl coating can be applied during relative movement between the needles 32 and the nozzles 30a, 30b. In some embodiments, one or more needles 32 may remain stationary while nozzles 30a, 30b move relative to needles 32 while spraying the coating. In other embodiments, a carrier strip, such as carrier strip 20 shown in Figure 2, or carrier strip 40 shown in Figures 3A and 3B, can move a plurality of surgical needles 32 with respect to opposing spray nozzles 30a, 30b while nozzles 30a, 30b remain stationary. In other embodiments, both the carrier strip 40 and the nozzles 30a, 30b can move relative to one another. Carrier strip 40 can be mounted below nozzles 30a, 30b as shown in Figure 3A, or carrier strip 40 can be mounted above nozzles 30a, 30b as shown in Figure 3B.
[0060] The speed of movement of the carrier strip 40 and/or the nozzles 30a, 30b can be controlled so that the spray nozzles 30a, 30b provide optimum coverage and coating of the needles 32. For example, the speed of relative movement between the needles 32 and nozzles 30a, 30b can be in the range of about 1 to about 15 inches per second. Ideally, the speed of relative motion can be in the range of about 3 inches per second to about 5 inches per second. Shields may optionally be disposed between the nozzle discharge openings 31a, 31b and the proximal portion of the needle.
[0061] In some embodiments, a single, homogeneous coating can be applied to a medical device, such as a surgical needle, using spray nozzles 30a, 30b. As noted above, when a single, homogeneous coating is used, it may be a mixture of the top and base coats described herein and/or a mixture of components designed to provide both slippery properties and durability. There are a number of ways in which the single, homogeneous coating can be applied using spray nozzles 30a, 30b. For example, the single, homogeneous coating can be pre-mixed with the correct weight ratio top and base coats, eg ratio of about 2:1, ratio 1:1, and/or ratio 1: 2, and the pre-mixed composition can be delivered from nozzles 30a, 30b in a single homogeneous coating layer on the medical device.
[0062] In another embodiment, the top coating may be delivered by one nozzle 30a, and the base coating may be provided by the other nozzle 30b. In the event that a ratio of about 2:1 of top and base coats is required, or a ratio of about 1:2 of top and base coats is needed, a nozzle 30a, 30b can be configured to delivering an amount of one coating, while the other nozzle 30b, 30a is configured to deliver a different amount (e.g., double or half the amount) of the other coating such that the weight ratios are as desired.
[0063] In yet a further modality, the top and base coatings can be provided in containers in fluid communication with the nozzles 30a, 30b and the two coatings can be mixed in the desired ratio inside the nozzles 30a, 30b, before applied to the medical device. For example, the nozzles 30a, 30b may have a mixing mechanism, such as two feed lines, associated with them that can mix a ratio of about 2:1, a ratio of 1:1, a ratio of 1:2, and/or any other desired ratio of the top and base coats so that the single, homogeneous coat is pre-mixed within the nozzles 30a, 30b, prior to being applied to the medical device.
[0064] There are many mechanisms known in the art for curing, tempering, and/or adjusting a coating on a surgical device such as a surgical needle. Curing can also cause any solvent used in the production of the coating to evaporate. Curing can generally be accomplished by exposing a coated surgical needle to some form of temperature rise and/or change in humidity for a predetermined period of time. For example, the coated needles can be placed in a furnace or oven, a hot box, a humidification chamber, and/or an infrared camera, among other ways known in the art. Cure times can range from the "fast" cure range of just a few seconds to times longer than twenty-four hours.
[0065] During the curing process, the temperature and/or humidity can be kept at a single value at all times and/or it can be increased or decreased as needed over time. The temperature can be monitored and adjusted using, for example, a thermocouple and a potentiometer to control the power in heating elements. The potentiometer can be pre-configured so that temperature measurements taken by the thermocouple in periodic increments over the length of the heating system are maintained at or within a specified temperature range. In other modalities, temperature can be controlled using a feedback loop in which temperature measurements that correlate to temperatures that surgical needles will pass are fed back to a power source that continuously adjusts the power released to the heated filaments to maintain a desired temperature range. A humidity monitor can be used to monitor and adjust humidity. In some modalities, each coating can be cured after applying it to the surgical needle. In other embodiments, all coatings can be applied before the curing process begins.
[0066] In one embodiment, an infrared emitter can be used to effect the cure of a coating. Infrared emitters are commercially available from Heraeus® Noblelight, eg Model SKL200-800. Actual emitters can include, for example, slender heated filaments 2.44 meters (eight feet) in length integrated into a reflective channel used to concentrate and contain heat. The infrared heating system can be oriented so that the opening of the channel faces downwards. Surgical needles to be cured in the infrared heating system can be held upright and passed between two reflective concave walls of the channel to about, say, % inch from the heated filaments. The needles can be held on a conveyor strip as they traverse the channel, at a speed in the range of about 3 inches per second to about 5 inches per second, although any speed can be used.
[0067] Although many methods for providing durable slippery coatings on surgical needles are contemplated, a flowchart of one modality of a particular method is illustrated in the Figure. 4A As shown, the method can include, in general, manufacturing the surgical needles, preparing the surface of the needles to receive a coating, coating the needles with a primer coat, base coat, and/or top coat, and cure the coatings. In another embodiment illustrated in Figure 4B, the method may generally include producing the surgical needles, preparing the surface of the needles for receiving a coating, optionally coating the needles with a primer coating, coating the needle with a single coating. and homogeneous, and cure the single homogeneous coating. One of skill in the art will understand the variations and additions that can be included in such methods.
[0068] When fabricating the surgical needles, raw wire of a suitable composition can be unwound and cut into raw blocks for formatting. Although rough blocks of any size can be used, depending on the size of the needle desired, in one modality, the yarn can be cut into two-inch rough blocks. Once cut, the blank blocks can be attached to a carrier strip of metal, such as that illustrated in Figure 2. The blank blocks can be secured and shaped into your preferred needle shape by any methods known in the art, including forming , crushing, bending, etc.
[0069] Needles that are properly shaped can be cleaned to remove contaminants and prepare the surface for receiving a coating. For example, needles can be exposed to high pressure nozzles that release water at high temperature and pressure. In other embodiments, needles can be baked at high temperatures to release any contaminants. Once the needles have been cleaned, they can be electrically polished for any amount of time needed. Needles can be immersed in the electric polishing bath (eg, sodium hydroxide, phosphoric acid, etc.) and subjected to direct current to remove ions at a controlled rate. Once finished, the needles can be rinsed successively, eg twice, in baths of deionized water.
[0070] In some embodiments, a primer coating, such as the SS4044P oppressor described above, can be applied to newly manufactured and cleaned surgical needles. Primer coating can be used, for example, when the needle is a tungsten-rhenium alloy. Primer can be applied using any method known in the art, including dipping or spraying, but in one modality, the primer is applied to surgical needles by dipping. Using a gripper or carrier strip, the needles can be immersed in the primer at room temperature for one to two seconds to fully cover them. One of skill in the art will understand that primers can be applied at any temperature and for any length of time as is appropriate for a particular primer. Reactive functional groups on the primer can react with the functional hydroxy groups on the surface of surgical needles and covalently bind to it. In some embodiments, after the primer coating has been applied, the surgical needle can be cured quickly for about 20 seconds at a suitable temperature, eg, about 200 degrees Celsius. Once cured, the primer can create a boundary between the surface of the surgical needle and any coatings applied later.
[0071] In some embodiments, a basecoat, such as the Momentive® basecoat described above, may be applied to the outer surface of the surgical needle, and over a primer if used, for example, the SS4044P primer. Any application method known in the art can be used, but in one embodiment, the surgical needle is sprayed or swirl coated with the base coat using opposing spray nozzles. For example, the surgical needle can be passed between opposite first and second spray nozzles to be coated. Applying the basecoat using spray or swirl coating ensures an evenly distributed layer of basecoat on the needle or over the primer, if used. As the basecoat is applied, the solvent, eg HFE solvent, can quickly evaporate to leave a thin layer of silicone evenly distributed on the needle surface. In some embodiments, the basecoat can be surface-cured by exposure to an "in-line" infrared heating system. The base coat can be exposed to a number of different wavelengths of infrared light and cured.
[0072] The coated medical device of the invention may also have a topcoat applied over the basecoat, more preferably after the basecoat is partially cured. For example, the NuSil® topcoat described above can be applied over the Momentive® basecoat. Any application method known in the art can be used, but in one embodiment, the surgical needle can be sprayed or swirl coated with the top coating using opposing spray nozzles. For example, the surgical needle can be passed between opposing third and fourth spray nozzles to be coated. Applying the topcoat using the spray or swirl coating technique ensures an evenly distributed layer of the topcoat over the basecoat. As the topcoat is applied, the solvent, eg HFE solvent, can quickly evaporate to leave a thin layer of topcoat evenly distributed over the basecoat. In some embodiments, after topcoat has been applied, the topcoat can be cured quickly to repel any excess solvent. Needles can be passed through, for example, a hot box or other heated curing system, at any time and at any temperature needed to effect evaporation of the solvent. In one embodiment, the topcoat can be rapidly cured in an infrared heater for approximately 20 seconds at a temperature in the range of about 165 degrees Celsius to about 200 degrees Celsius.
[0073] In other embodiments, a single, homogeneous coating may be applied to the outer surface of the surgical needle, and over a primer if used, for example, the SS4044P primer. The single, homogeneous coating can be, for example, a combination of the Momentive® basecoat and the Nu-Sil® topcoat described above, although any suitable combination of materials can be used to form the single, homogeneous coating. Any application method known in the art can be used, but in one embodiment, the surgical needle is sprayed or swirl coated with the single, homogeneous coating using opposing spray nozzles. For example, the surgical needle can be passed between opposite first and second spray nozzles to be coated. Applying the single, homogeneous coating using spray or swirl coating ensures an evenly distributed layer of the single, homogeneous coating on the needle or over the needle's primer coating, if used. As the single, homogeneous coating is applied, the solvent, eg HFE solvent, can quickly evaporate to leave a thin layer of the single, homogeneous coating on the needle surface. In some embodiments, the single, homogeneous coating can be cured by exposure to an in-line infrared heating system for a sufficiently effective period of time, for example, from about 1 second to about 60 seconds, from about 10 seconds to about 30 seconds, and/or for about 20 seconds. The single, homogeneous coating can be exposed to a number of different wavelengths of infrared light and cured. The single, homogeneous coating can also be cured in an oven at a temperature in the range of about 60 degrees Celsius to about 180 degrees Celsius, for a period of time in the range of about 1 hour to about 5 hours, of about from 2.5 hours to about 3.5 hours, and/or more preferably for about 3 hours at a temperature in the range of about 100 degrees Celsius to about 140 degrees Celsius.
[0074] After the application of the top coating and/or the single and homogeneous coating, the surgical needles can be optionally rewound. In some modalities, coated surgical needles may be exposed to a final healing process. For example, rewound needles can be placed inside a convection oven and cured at a temperature and time sufficient to further cure the coating. In one embodiment, surgical needles can be cured in a convection oven for approximately four hours at about 165 degrees Celsius. In other embodiments, the final cure can be performed at a temperature of about 80 degrees Celsius for approximately three hours.
[0075] The cure times for the coatings and exemplary methods described herein are extremely beneficial in that they are significantly shorter than the cure times for coatings and methods previously known in the art. Previous coatings and methods could require the surgical needles to cure for up to 72 hours plus processing and coating time. The coatings and exemplary methods described here can reduce the total cure time to less than about 4 hours and possibly less than about 15 minutes, providing a significant increase in needle manufacturing efficiency. By using the single, homogeneous coating, the cure time can be further reduced to less than about 1 minute.
[0076] The use of two coatings, as described above, and/or a single coating, for example continuous as also described above, results in surgical needles that exhibit reduced and/or generally constant tissue penetration force compared to surgical needles after an equivalent number of passes through the tissue. Thus, the lubricity of the needle as well as the durability of the coating is improved. This effect is understood to result in a number of reasons. For example, applying the base and top coatings using a swirl coating process provides an even distribution of the coatings over the substrate. This is most clearly represented in Figure 6, which will be described in more detail below. In addition, coating compositions in combination with the present invention's application and curing methods can result in significantly lower average force required to repeatedly pass the needle through synthetic media, as shown in Figure 7, which will also be described in larger details below.
[0077] The use of the optional primer coating can also be beneficial. A primer coating may be able to chemically bond to the needle surface to provide a bonding substrate for slippery silicone coatings to adhere to, resulting in increased durability of the base and top coatings. For example, Figure 5 illustrates the force required to pass a needle through the synthetic medium in relation to the number of passes through the synthetic medium. As shown, unprimed needles have a drastic increase in force required after thirty passes when compared to primer-coated needles of identical material and configuration, which tend to maintain a reasonably constant force up to at least thirty passes through the synthetic medium. More details will be presented in the examples described below.
[0078] Coating performance for medical devices can generally be tested with a variety of conventional tests. In the case of surgical needles, coating performance and integrity is assessed using a penetration testing device. A portion of a coated surgical needle is retained using a gripping device, and the coated needle then partially passes through a penetrable synthetic or natural material a number of times. The material is typically a type of polymer or synthetic leather, eg Permair, Rubber-Cal, Monmouth rubber, Porvair, etc. The needle may be passed through the penetrable material from about one to about twenty times, between about one to about twenty-five times, and most preferably between about one to about thirty times. The needle is then retracted from the middle. Maximum force is recorded during each pass and is used as a measure of coating performance. Various coating performance attributes can be tested using these techniques.Examples
[0079] The following experiments were conducted to examine the effects of variation in needle coating materials and methods. For each test, needles were passed through Monmouth Duraflex MR40 NBR rubber membrane ("Monmouth rubber"), which serves to simulate flesh, or human cadaver tissue. In the non-limiting examples below, from 4 to 10 needles were used and individually passed through the penetration membrane thirty times each. The maximum force in grams was recorded during each pass and used as a measure of coating performance.
[0080] The surgical needles were mounted in a rotary stage to fix the needle in a position perpendicular to the surface of the penetration membrane and oriented in its radial profile with the geometric axis of rotation in the same plane as the plane of the penetration membrane. The needle was rotated inside the penetration membrane, which was mounted on top of the load cell. The maximum amount of vertical force was recorded as the needle was pushed through the penetration membrane.
[0081] The following non-limiting examples serve to further illustrate the principles and practices of the present invention: Example 1
[0082] The following tests were performed to examine the effect that coating methods have on the force required to pass a needle through Monmouth synthetic rubber media. The performance of needles that were dip coated was compared to the performance of needles that were spray/swirl coated. Test A
[0083] In Test A, five needles were prepared for the penetration test. The needles are made of ETHALLOY® stainless steel alloy and have a diameter of 0.0105 inches. A basecoat composition was prepared from a 20 wt% blend of Micropro 600 and Micromatte 2000, produced by Micropowders Inc., blended with 80 wt% HFE-72DE solvent. The powder weight ratio of MicroPro and Micromatte was 4:1. Five test needles were each dipped into the base coat to coat their surfaces. The needles were coated by hand through the immersion process and placed in a magnetic tray. The tray includes raised magnetic strips to retain the proximal ends of the trapped needles during the cure cycle and transport while the distal end (tip) of the needles hover over the edge of the magnetic strips. This setting prevents the needle tips from contacting the tray. The coated needles were then heated to 190 degrees Celsius in a convection oven for ninety minutes in an ambient atmosphere. The needles were then left to cool naturally to room temperature outside the oven.
[0084] A topcoat composition was prepared using 26% by weight of NuSil® MED4162 with 74% by weight of HFE-72DE solvent. The five needles were then each immersed by hand into the topcoat composition. The needles were then heated to 220 degrees Celsius in a convection oven and cured for four hours in an ambient atmosphere. The needles were left to cool naturally to room temperature outside the oven.
[0085] Once cured, the five needles were each passed through the penetration membrane thirty times and the penetration force in grams was recorded as shown in Table 1 below.

[0086] In Test B, five needles were prepared for the penetration test. The needles are made of ETHALLOY® stainless steel alloy and have a diameter of 0.0105 inches. A basecoat composition was prepared from a 20 wt% blend of Micropro 600 and Micromatte 2000, produced by Micropowders Inc., blended with 80 wt% HFE-72DE solvent. The powder weight ratio of MicroPro and Micromatte was 4:1. The five test needles were swirl coated with the basecoat composition using a single-pass spray using the SC-300 Swirl Coat™ applicator and the Conformal Century® C-341 coating system available from Asymtek® of Carlsbad, AC with the following parameters: 2 psi hydrostatic pressure, 50 PSI air assist, and 10 inches/second line speed. The coated needles were then heated to 190 degrees Celsius in a convection oven and cured for ninety minutes in an ambient atmosphere. The needles were left to cool naturally to room temperature outside the oven.
[0087] A topcoat composition was prepared using 26% by weight of NuSil® MED4162 with 74% by weight of HFE-72DE solvent. The five test needles were swirl coated with the topcoat composition using a single pass spray with the following parameters: 10 psi hydrostatic pressure, 50 PSI air assist, and 5 inches/second of line speed. The needles were then cured for four hours at 220 degrees Celsius. Once cured, the five needles were each passed through the penetration membrane thirty times and the penetration force in grams was recorded as shown in Table 2 below.

[0088] Figure 6 is a graphical representation of the average of the results of Tests A and B in direct comparison. The y axis shows the penetration force in grams required to pass a needle through the penetration membrane. The geometric x axis shows the number of passes. The thick solid line represents needles that have been dip coated with the base and topcoat compositions as shown in Test A, while the thin solid line represents needles that have been swirl coated with the basecoat and topcoat compositions. top, as shown in Test B.
[0089] As can be seen, the needles that were dip coated had an initial penetration force of about 38 g. Penetration force steadily increased during the thirty passes, and the needles required a mean maximum force of 61 g after thirty passes. In contrast, needles that were swirl coated had an initial penetration force of about 31 g. The penetration force remained substantially constant throughout the thirty passes, with the average maximum force after thirty passes being about 40 g. As shown, needles that were swirl coated required about 7 g less force at first on average than needles that were dip coated, and the force remained substantially constant. Ultimately, swirl-coated needles required about 21 g less maximum force after thirty passes than dip-coated needles.Example 2
[0090] The penetration performance of various coating compositions and coating methods were also tested. In tests A and B below, two different types of needle coating compositions and application methods were examined. The needles were passed through a synthetic Monmouth rubber medium. Test A
[0091] In Test A, ten commercially available Ethicon BV-175 surgical needles that have a diameter of 0.0078 inch were tested. A coating was applied using a double dip procedure. In particular, a silicone dip was prepared using a concentration of NuSil®, Product No. MED4162, mixed with Micropro 600 and Micromatte 2000 powders for lubrication as described above. The needles were placed on a moving carrier strip and immersed for the first time. The needles were then rapidly cured in a hot box at approximately 225 degrees Celsius for thirty seconds. The needles were then cured for 36 hours in a convection oven at 163 degrees Celsius. The needles were immersed a second time, quickly cured, and then cured in a convection oven for another 36 hours.
[0092] As shown in Table 3 below, ten needles were tested with thirty passes through the penetration membrane.
Test B
[0093] In Test B, ten Ethiconque tungsten-rhenium alloy needles having a diameter of 0.008 inch were tested. Needles were prepared by applying Momentive® SS4044P primer coating at room temperature. The primer coating was rapidly cured at 200 degrees Celsius for 2-3 seconds. A basecoat composition was then applied during priming using swirl coating techniques. The basecoat composition was made by combining 27.58% by weight of Momentive®, vinyl siloxane polymer, Product No. MSC2631, with 72.25% by weight of the solvent HFE 72-DE and stirred for about five minutes. Momentive®, catalyst in toluene, Product No. SS8010, was then added to the mixture at 0.02% by weight, and Momentive®, polymethyl hydrogen siloxane, Product No. SS4300 was added at 0.14% by weight . Basecoat was applied to the surgical needles using the Asymtek C-341 conformal coating applicator and the Asymtek SC-300 swirl applicator. The needles were then heated to 300 degrees Celsius for thirty seconds in an infrared heater.
A topcoat composition was then applied to the needles and was formed from 26% by weight of NuSil® MED4162 silicone product combined with 74% by weight of HFE 72-DE solvent. The topcoat composition was also applied using swirl coating techniques with the Asymtek C-341 conformal coater and the Asymtek SC-300 swirl applicator. The needles were again rapidly cured at a temperature of 190 degrees Celsius for approximately thirty seconds.
[0095] The needles included in Test B were then packaged cured at 80 degrees Celsius for three hours in a convection oven. Needles were tested by passing each needle thirty times through the penetration membrane. The force required to perform tallation is shown in Table 4.

[0096] Figure 7 is a graphical representation of the average of the results of Tests A and B in direct comparison. The y axis shows the penetration force in grams required to pass a needle through the penetration membrane. The geometric x axis shows the number of passes. The thick solid line represents the conventional dip coated needles as shown in Test A, while the thin solid line represents the spray coated needles according to the present invention as shown in Test B.
[0097] As shown, the Test A needles initially required an average penetration force of about 29 g. The average penetration force for Test A needles increased to 39 g after thirty passes. Test B needles had an initial average penetration force of 21 g and an average penetration force of 25 g after thirty passes.
[0098] The following tests were performed to examine the effect that coating methods have on the force required to pass a needle through Monmouth synthetic rubber media. The performance of needles that were dip coated was compared to the performance of needles that were spray/swirl coated. Test A
[0099] In test A, four 0.6604mm (0.026 inch) diameter needles made from ETHALLOY® alloy and with a tapered cutting point geometry were prepared for the penetration test. A basecoat composition was prepared from a solution of 2.5 g of Momentive®, vinyl polymer MSC2631 siloxane, Product no., 22.15 g of Exxon Isopar-K, 0.0022 g of Momentive®, catalyst in toluene, Product No. SS8010, and 0.0127 of Momentive®, polymethyl hydrogen siloxane, Product No. SS4300. Four test needles were each dipped into the basecoat composition to coat their surfaces. The coated needles were then heated to 200 degrees Celsius in a convection oven type furnace for one hour.
A composition to coat the topcoat was prepared using 2.50 g of NuSil® MED4162 with 22.50 g of Exxon Isopar-K. The four needles were then each dipped into the topcoat composition. The needles were then heated to 140 degrees Celsius in a convection oven and cured for three hours.
[00101] Once cured, the four needles were each passed through the penetration membrane thirty times and the penetration force in grams was recorded as shown in Table 5 below.
Test B
[00102] In test B, five 0.6604mm (0.026 inch) diameter needles produced from ETHALLOY® alloy and with a tapered cutting point geometry were prepared for the penetration test. Needles were prepared by applying a basecoat composition using swirl coating techniques. The basecoat composition was made by combining 27.58% by weight of Momentive®, vinyl siloxane polymer, Product No. MSC2631, with 72.25% by weight of the solvent HFE 72-DE and stirred for about five minutes. Momentive®, catalyst in toluene, Product No. SS8010, was then added to the mixture at 0.02% by weight, and Momentive®, polymethyl hydrogen siloxane, Product No. SS4300 was added at 0.14% by weight. Basecoat was applied to the surgical needles using the Asymtek C-341 conformal coating applicator and the Asymtek SC-300 swirl applicator. The needles were then heated to 300 degrees Celsius for thirty seconds in an infrared heater.
[00103] A topcoat composition was then applied to the needles and was formed from 26% by weight of NuSil® MED4162 silicone product combined with 74% by weight of HFE 72-DE solvent. The topcoat composition was also applied using swirl coating techniques with the Asymtek C-341 conformal coater and the Asymtek SC-300 swirl applicator. The needles included in Test B were then batch cured at 140 degrees Celsius for three hours in a convection oven.
[00104] Once cured, the five needles were each passed through a synthetic Monmouth rubber medium thirty times and the penetration force in grams was recorded as shown in Table 6 below.

[00105] Figure 8 is a graphical representation of the average of the results of Tests A and B in direct comparison. The y axis shows the penetration force in grams required to pass a needle through the penetration membrane. The geometric x axis shows the number of passes. The square dots represent the dip coated needles as shown in Test A, while the diamond dots represent the spray coated needles in accordance with the present invention as shown in Test B.
[00106] As shown, Test A needles with the dip coating initially required an average penetration force of 62 g. The average penetration force for Test A needles increased by 115 g after thirty passes. Test B spray coated needles performed with an initial average penetration force of 58 g and resulted in an average penetration force of 64 g after thirty passes. As can be seen, the needles in Test B with the spray coating required significantly less penetration force up to thirty passes.
[00107] The penetration performance of various coating compositions and coating methods was tested. In tests A, B and C below, three different types of needle coating compositions and application methods were examined. The penetration material for these tests was human cadaver carotid artery tissue. Test A
[00108] In Test A, commercially available Ethicon BV-1 surgical needles that have a diameter of 0.0105 inch were tested. A coating was applied using the procedures associated with the fabrication of this series. In particular, a silicone dip was prepared using a concentration of NuSil®, Product No. MED4162. The needles were placed on a moving vehicle strip and immersed for the first time. The needles were then rapidly cured in a hot box at approximately 190 degrees Celsius for twenty seconds. The needles were dipped a second time and quickly cured again with the same settings as above. Finally, the needles were immersed a third time and then cured in a convection oven for 8 to 16 hours at 190 degrees Celsius. Test B
[00109] In test B, Ethicon tungsten-rhenium alloy needles having a diameter of 0.0105 inch were tested. Needles were prepared by applying Momentive® SS4044P primer coating at room temperature. A basecoat composition was then applied during priming using swirl coating techniques. The basecoat composition was made by combining 27.58% by weight of Momentive®, vinyl siloxane polymer, Product No. MSC2631, with 72.25% by weight of the solvent HFE 72-DE and stirred for about five minutes. Momentive®, catalyst in toluene, Product No. SS8010, was then added to the mixture at 0.02% by weight, and Momentive®, polymethyl hydrogen siloxane, Product No. SS4300 was then added at 0.14% by weight . Basecoat was applied to the surgical needles using the Asymtek C-341 conformal coating applicator and the Asymtek SC-300 swirl applicator. The needles were then heated to 300 degrees Celsius for thirty seconds in an infrared heater.
[00110] A topcoat composition was then applied to the needles and was formed from 26% by weight of the silicone product NuSil® MED4162 combined with 74% by weight of the solvent HFE 72-DE. The topcoat composition was also applied using swirl coating techniques with the Asymtek C-341 conformal coater and the Asymtek SC-300 swirl applicator.
[00111] The needles included in Test B were then batch cured at 80 degrees Celsius for three hours in a convection oven. The needles were tested by passing each needle thirty times through the penetration membrane. Test C
[00112] In Test C, a competitive brand of commercially available surgical needles (0.010 inch diameter) were tested out of the package. Needles were tested by passing each needle thirty times through the penetration membrane.
[00113] Figure 9 is a graphical representation of the median results of Tests A, B and C in direct comparison The geometric y axis shows the penetration force in grams required to pass a needle through human cadaver tissue. The geometric x axis shows the number of passes. The triangular dots represent conventional dip coated needles as shown in Test A above. The circular dots represent needles prepared in accordance with the present invention as shown in Test B above. Diamond stitches represent the competing brand of needles as shown in Test C above.
[00114] As shown, commercially available Test A needles that have a dip coating initially required an average penetration force of about 16 g. The average penetration force for Test A needles increased to about 18 g after thirty passes. Test B needles with the coating according to the present invention were performed with an initial average penetration force of about 13 g and maintained that penetration force after thirty passes. Competing brand of needles were performed with an initial average penetration force of about 15 g and resulted in an average penetration force of about 25 g after thirty passes. As can be seen, the needles in Test B required significantly less penetration force up to thirty passes.
[00115] The use of two coatings, as described above with respect to the present invention, results in surgical needles that exhibit reduced tissue penetration force compared to conventional surgical needles after an equivalent number of passes through tissue. Thus, the lubricity of the needle as well as the durability of the coating is improved. This is understood to result in a number of reasons. For example, applying the base and top coatings using a swirl coating process provides an even distribution of the coatings over the substrate. Furthermore, the composition of coatings in combination with the present invention's application and curing methods can result in significantly decreased average force required to repeatedly pass the needle through the fabric. Cure time is also significantly shortened, resulting in more efficient manufacturing processes.Example 6
[00116] The penetration performance of a medical device coated with a single homogeneous coating was tested against the performance of a medical device coated with both top and bottom coatings. In tests A, B and C below, two different types of needle coating compositions and application methods were examined. The needles were passed through Monmouth synthetic rubber medium. Tests A, B and C
[00117] In Tests A, B, and C, ten commercially available Ethicon-2 surgical needles that have a diameter of 0.6096cm (0.024 inch) were tested. The ten test needles in each test were coated with a single, homogeneous coating. In test A, the single, homogeneous coating was composed of a mixture of "Component A" formed from 18.38% of the organopolysiloxane functionalized with vinyl, ie, Momentive® Product Code No. MSC2631 si-licone produced by Momentive® Performance Materials of Waterford, NY8.667, and 18.38 a hydroxyl terminated polydimethylsiloxane, ie, NuSil® Technologies Silicone Product No. MED4162 produced by NuSil® Technologies of Carpentaria, CA, 72.85% HFE solvent, 0.0165 catalyst and 0.0936% crosslinker. The Component A blend was equivalent to a 2:1 ratio of the basecoat and topcoat solutions and was blended from master batches of the basecoat and topcoat solutions.
[00118] In test B, the single, homogeneous coating was composed of a mixture of "Component B" formed from 13.78% of the vinyl-functionalized organopolysiloxane, ie, Momentive® Product Code No. MSC2631 silicone produced by Momentive ® Performance Materials of Waterford, NY, 13.00% hydroxyl terminated polydimethylsiloxane, ie, NuSil® Technologies Silicone Product No. MED4162 produced by NuSil® Technologies of Carpentaria, CA, 73.13% HFE solvent, 0.0124% of catalyst and 0.0702% of crosslinker. The Component B blend was equivalent to a 1:1 ratio of basecoat and topcoat solutions and was blended from master batches of the basecoat and topcoat solutions.
[00119] In test C, the single homogeneous coating was composed of a mixture of "Component C" formed from 9.189% of the vinyl-functionalized organopolysiloxane, ie, Momentive® Product Code No. MSC2631 silicone produced by Momentive® Performance Materials of Waterford, NY, 17.33% hydroxyl terminated polydimethylsiloxane, ie, NuSil® Technologies Silicone Product No. MED4162 produced by NuSil® Technologies of Carpentaria, CA, 73.42% HFE solvent, 0.0083% catalyst and 0.0468% crosslinker. The Component C blend was equivalent to a 1:2 ratio of the basecoat and topcoat solutions and was blended from master batches of the basecoat and topcoat solutions.
[00120] The ten test needles in each test were swirl coated with the single, homogeneous coating composition using a single-pass spray using the SC-300 Swirl Coat™ applicator and available Conformal Century® C-341 coating system from Asymtek® of Carlsbad, CA with the following parameters: 10 psi hydrostatic pressure, 50 psi air assist, and a needle valve with a setting of 8. The coated needles were then heated to approximately 200 degrees Celsius in a heater by infrared for 20 seconds in ambient atmosphere.
[00121] As shown in tables 7 to 9 below, the ten needles of each of tests A, B and C were tested with thirty passes through the penetration membrane.




[00122] In Test D, ten commercially available Ethicon-2 surgical needles that have a diameter of 0.6096cm (0.024 inch) were tested. Needles were prepared by applying a basecoat composition using the swirl coating techniques and parameters described above in tests A, B and C. The basecoat composition was produced by combining 27.58% by weight of Momentive® vinyl functionalized base polymer, product no. MSC2631, with 72.25% by weight of HFE 72-DE solvent. Momentive® catalyst in toluene, Product No. SS8010, was then added to the mixture at 0.02% by weight, and Momentive® polymethyl hydrogen siloxane, Product No. SS4300 was then added at 0.14% by weight. Basecoat was applied to the surgical needles using the Asymtek C-341 conformal coating applicator and the Asymtek SC-300 swirl applicator. The needles were then heated to 300 degrees Celsius for thirty seconds in an infrared heater.
[00123] A topcoat composition was then applied to the needles and was formed from 26% by weight of NuSil® MED4162 silicone product combined with 74% by weight of HFE 72-DE solvent. The topcoat composition was also applied using swirl coating techniques with the Asymtek C-341 conformal coater and the Asymtek SC-300 swirl applicator.
[00124] The needles included in Test D were then batch cured at 140 degrees Celsius for three hours in a convection oven. Needles were tested by passing each needle thirty times through the penetration membrane. The force required to perform such action is shown in Table 10.

[00125] Figure 10 is a graphical representation of the median results of Tests A, B and C in direct comparison The geometric y axis shows the penetration force in grams required to pass a needle through the penetration membrane. The geometric x axis shows the number of passes.
[00126] As can be seen, needles that were coated with a single, homogeneous coating had an initial penetration force of about 41 g in Tests A and B and about 40 g in Test C. The penetration force increased by one little over the thirty passes, and the needles required an average maximum force of about 65 g in Tests A and B and about 67 g in Test C, after thirty passes. In contrast, needles that were coated with the two coats, i.e. the base coat and the top coat, had an initial penetration force of about 46 g. The average maximum penetration force after thirty passes was about 61 g. As shown, needles that were coated with a single, homogeneous coating initially required about 5g to 6g less force, on average, than needles that were coated with two layers.
[00127] The use of a single, homogeneous coating as described above with respect to the results of the present invention results in surgical needles that exhibit reduced initial tissue penetration force compared to two-layer surgical needles and standard surgical needles after a equivalent number of passes through the fabric. Thus, the lubricity of the needle as well as the durability of the coating is improved. This is understood to result in a number of reasons. For example, applying a single, homogeneous coating using a swirl coating process provides a fine and even distribution of coatings over the substrate. Furthermore, the coating composition in combination with the present invention's application and curing methods can result in the significantly decreased average force required to repeatedly pass the needle through the tissue. The cure time is also significantly shorter compared to the cure time required when two coats such as the top coat and base coat are used, resulting in more efficient manufacturing processes.
[00128] A person skilled in the art will appreciate other aspects and advantages of the invention based on the embodiments described above. Accordingly, the invention is not to be limited by what has been particularly shown and described, except as indicated by the appended claims. All publications and references cited herein are expressly incorporated herein by reference in their entirety.

权利要求:
Claims (11)
[0001]
1. A method of coating a medical device (10), comprising: providing a medical device (10); coating, using a swirl coating process, to provide an even distribution of coatings on the substrate; at a temperature in the range of 60 °C to 180 °C for a period of time in the range of 1 hour to 5 hours; characterized by the fact that it further comprises the step of: applying a single, homogeneous coating to at least a part of a medical device surface (10) with a thickness in the range of 1 micrometer to 12 micrometers, where the single homogeneous coating is a combination of a vinyl-functionalized organopolysiloxane and a polydimethylsiloxane.
[0002]
2. Method according to claim 1, characterized in that the application of a homogeneous coating to a surface of the medical device (10) includes applying a coating with a thickness in the range of 1 micrometer to 3.5 micrometers.
[0003]
3. Method according to claim 1 or 2, characterized in that the surface of the medical device (10) includes a primer comprising a silicone.
[0004]
4. Method according to any one of claims 1 to 3, characterized in that the medical device (10) is formed of a tungsten alloy, a refractory alloy, stainless steel, nitinol and tantalum.
[0005]
5. Method according to claim 4, characterized in that the medical device (10) is formed from a tungsten-rhenium alloy.
[0006]
6. Method according to any one of claims 1 to 5, characterized in that the application of a homogeneous coating includes distributing the homogeneous coating to the surface of the medical device (10) in a high vapor pressure, low point solvent of boiling.
[0007]
7. Method according to claim 6, characterized in that the high vapor pressure, low boiling point solvent is a hydrofluorinated ether solvent.
[0008]
8. A method according to any one of claims 1 to 7, characterized in that providing a medical device (10) includes providing an elongated medical device (10) having a tissue penetrating portion (12).
[0009]
9. Method according to any one of claims 1 to 8, characterized in that the application of the homogeneous coating includes spraying the homogeneous coating on the surface of the medical device (10).
[0010]
10. Method according to any one of claims 1 to 9, characterized in that it further comprises curing the homogeneous coating on the surface of the medical device (10) for a time in the range of 10 seconds to 30 seconds.
[0011]
11. Medical device (10) characterized in that it is obtained through the method as defined in any one of claims 1 to 10.

类似技术:

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BR112012010995B1|2021-08-17|METHOD FOR COATING A MEDICAL DEVICE AND MEDICAL DEVICE

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引用文献:

---

公开号 | 申请日 | 公开日 | 申请人 | 专利标题

---

---

US1944823A|1930-10-28|1934-01-23|Nat Electric Prod Corp|Method and means for coloring and coating wires and the like|

---

US4256870A|1979-05-17|1981-03-17|General Electric Company|Solventless release compositions, methods and articles of manufacture|

---

US4806430A|1985-12-03|1989-02-21|Becton, Dickinson And Company|Film-forming silicone compositions having lubricating properties|

---

US4720521A|1985-12-03|1988-01-19|Becton, Dickinson And Company|Film-forming silicone compositions having lubricating properties|

---

JPH0620461B2|1989-08-24|1994-03-23|株式会社松谷製作所|Suture needle and method for manufacturing the suture needle|

---

US5258013A|1991-01-07|1993-11-02|United States Surgical Corporation|Siliconized surgical needle and method for its manufacture|

---

JP3124564B2|1991-02-21|2001-01-15|マニー株式会社|Medical suture needle and manufacturing method thereof|

---

ES2152957T3|1993-05-13|2001-02-16|American Cyanamid Co|SILICONE WATERPROOF COMPOSITIONS FOR COATING, METHOD FOR COATING SUBSTRATES WITH THE SAME AND SURGICAL NEEDLES COVERED IN THIS MODE.|

---

US5429682A|1993-08-19|1995-07-04|Advanced Robotics Technologies|Automated three-dimensional precision coatings application apparatus|

---

US5447465A|1993-08-19|1995-09-05|United States Surgical Corporation|Method of treating needle blanks|

---

US6018860A|1996-06-07|2000-02-01|Ethicon, Inc.|Process for manufacturing drilled taper point surgical needles|

---

US5463010A|1993-11-12|1995-10-31|Surface Engineering Technologies, Division Of Innerdyne, Inc.|Hydrocyclosiloxane membrane prepared by plasma polymerization process|

---

GB2292808B|1994-08-16|1998-04-08|Phisilog Res Ltd|Final production and testing of motor controllers|

---

US6335383B1|1994-10-18|2002-01-01|Ethicon, Inc.|Microdispersions for coating surgical devices|

---

US6017577A|1995-02-01|2000-01-25|Schneider Inc.|Slippery, tenaciously adhering hydrophilic polyurethane hydrogel coatings, coated polymer substrate materials, and coated medical devices|

---

US5688598A|1996-06-28|1997-11-18|Morton International, Inc.|Non-blistering thick film coating compositions and method for providing non-blistering thick film coatings on metal surfaces|

---

US6325853B1|1996-07-19|2001-12-04|Nordson Corporation|Apparatus for applying a liquid coating with an improved spray nozzle|

---

US7229413B2|1996-11-06|2007-06-12|Angiotech Biocoatings Corp.|Echogenic coatings with overcoat|

---

US5997517A|1997-01-27|1999-12-07|Sts Biopolymers, Inc.|Bonding layers for medical device surface coatings|

---

DE19722880C1|1997-05-24|1998-11-19|Ethicon Gmbh|Process for coating surgical needles|

---

TW384505B|1997-07-04|2000-03-11|Tokyo Electron Ltd|Coating device|

---

US5911711A|1998-06-29|1999-06-15|Becton, Dickinson And Company|Lubricant system for hypodermic needles and method for its application|

---

US6252195B1|1999-04-26|2001-06-26|Ethicon, Inc.|Method of forming blind holes in surgical needles using a diode pumped Nd-YAG laser|

---

US6610035B2|1999-05-21|2003-08-26|Scimed Life Systems, Inc.|Hydrophilic lubricity coating for medical devices comprising a hybrid top coat|

---

US6231990B1|1999-06-21|2001-05-15|General Electric Company|Adhesion primer for use with RTV silicones|

---

US6908624B2|1999-12-23|2005-06-21|Advanced Cardiovascular Systems, Inc.|Coating for implantable devices and a method of forming the same|

---

JP4144019B2|2000-01-07|2008-09-03|ニプロ株式会社|Puncture needle|

---

US20050226993A1|2000-10-03|2005-10-13|Nawrocki Jesse G|Medical devices having durable and lubricious polymeric coating|

---

US20060190040A1|2001-09-27|2006-08-24|Roby Mark S|Coated surgical needles|

---

US20050240223A1|2001-09-27|2005-10-27|Roby Mark S|Siliconized surgical needles and methods for their manufacture|

---

US6936297B2|2001-09-27|2005-08-30|Tyco Healthcare Group, Lp|Siliconized surgical needles and methods for their manufacture|

---

US6558409B1|2001-09-28|2003-05-06|Tyco Healthcare Group Lp|Plasma treated surgical needles and methods for their manufacture|

---

US6765069B2|2001-09-28|2004-07-20|Biosurface Engineering Technologies, Inc.|Plasma cross-linked hydrophilic coating|

---

US7015262B2|2002-05-01|2006-03-21|Lifescan, Inc.|Hydrophilic coatings for medical implements|

---

DE10224128A1|2002-05-29|2003-12-18|Schmid Rhyner Ag Adliswil|Method of applying coatings to surfaces|

---

AT470461T|2002-07-24|2010-06-15|Covidien Ag|METHOD FOR THE LUBRICATION OF INJECTION NEEDLES WITH RADIATION-CURABLE SILICONE MATERIAL|

---

US20040040467A1|2002-08-27|2004-03-04|Thomas Raymond H.|Silicone based compositions|

---

US7041088B2|2002-10-11|2006-05-09|Ethicon, Inc.|Medical devices having durable and lubricious polymeric coating|

---

JP4110973B2|2003-01-17|2008-07-02|Ｊｓｒ株式会社|Composition for forming silicon-aluminum mixed film, silicon-aluminum mixed film and method for forming the same|

---

US7001421B2|2003-02-28|2006-02-21|Medtronic Vascular, Inc.|Stent with phenoxy primer coating|

---

US20040260269A1|2003-06-23|2004-12-23|Yair Assaf|Method for treating false aneurysm and a needle for use in such a method|

---

US20040266302A1|2003-06-30|2004-12-30|Disalvo Anthony L.|Absorbent article having odor control properties|

---

US7060319B2|2003-09-24|2006-06-13|Boston Scientific Scimed, Inc.|method for using an ultrasonic nozzle to coat a medical appliance|

---

US7028867B2|2003-10-30|2006-04-18|Nordson Corporation|Conformal coating applicator and method|

---

US20050158470A1|2003-11-11|2005-07-21|Nicholas Maiorino|Spray head applicator, dispensing systems, and methods of use|

---

US8007737B2|2004-04-14|2011-08-30|Wyeth|Use of antioxidants to prevent oxidation and reduce drug degradation in drug eluting medical devices|

---

JP2005306902A|2004-04-16|2005-11-04|Asahi Glass Co Ltd|Silicone solution for coating and method for coating silicone compound|

---

CA2588080C|2004-11-18|2013-01-08|3M Innovative Properties Company|Masking method for coating a microneedle array|

---

US8323333B2|2005-03-03|2012-12-04|Icon Medical Corp.|Fragile structure protective coating|

---

JP2007024625A|2005-07-14|2007-02-01|Yazaki Corp|Voltage measurement method and voltage measurement device|

---

US7914809B2|2005-08-26|2011-03-29|Boston Scientific Scimed, Inc.|Lubricious composites for medical devices|

---

US20070060952A1|2005-09-02|2007-03-15|Roby Mark S|Surgical stapling device with coated knife blade|

---

US8166909B2|2005-11-15|2012-05-01|Surmodics, Inc.|Apparatus and methods for applying coatings|

---

US20070149629A1|2005-12-22|2007-06-28|Michael Stephen Donovan|Expanded and expandable high glass transition temperature polymers|

---

US7758908B2|2006-03-28|2010-07-20|Boston Scientific Scimed, Inc.|Method for spray coating a medical device using a micronozzle|

---

US8075995B2|2006-03-30|2011-12-13|Becton, Dickinson And Company|Coating system, articles and assembly using the same and methods of reducing sticktion|

---

US20070254091A1|2006-04-28|2007-11-01|Boston Scientific Scimed, Inc.|System and method for electrostatic-assisted spray coating of a medical device|

---

US8791254B2|2006-05-19|2014-07-29|3M Innovative Properties Company|Cyclic hydrofluoroether compounds and processes for their preparation and use|

---

JP2008000287A|2006-06-21|2008-01-10|Terumo Corp|Sliding composition for coating medical appliance and medical appliance with sliding coat|

---

JP4813298B2|2006-08-31|2011-11-09|マニー株式会社|Manufacturing method of eyeless suture needle|

---

EP2061529B1|2006-09-15|2013-07-24|Becton, Dickinson & Company|Medical components having coated surfaces exhibiting low friction and methods of reducing sticktion|

---

US8193397B2|2006-12-06|2012-06-05|3M Innovative Properties Company|Hydrofluoroether compounds and processes for their preparation and use|

---

US9358000B2|2006-12-15|2016-06-07|Ethicon, Inc.|Tungsten alloy suture needles|

---

JP5293989B2|2007-07-24|2013-09-18|ノードソン株式会社|Small liquid spray equipment|

---

CA2638310A1|2007-08-23|2009-02-23|Tyco Healthcare Group Lp|Swirl coating applicator|

---

DE102007059755A1|2007-12-10|2009-06-18|Biotronik Vi Patent Ag|Implants with membrane diffusion controlled drug release|

---

KR101498004B1|2008-01-10|2015-03-03|에디컨인코포레이티드|Tungsten alloy suture needles|

---

US8557328B2|2009-10-02|2013-10-15|Ppg Industries Ohio, Inc.|Non-orthogonal coater geometry for improved coatings on a substrate|

---

US9259219B2|2009-11-09|2016-02-16|Ethicon, Llc|Surgical needle coatings and methods|

---

US9332982B2|2009-11-09|2016-05-10|Ethicon, Llc|Surgical needle coatings and methods|

---

US9221075B2|2009-11-09|2015-12-29|Ethicon, Inc.|Surgical needle coatings and methods|

---

US8865247B2|2009-12-18|2014-10-21|Ethicon, Inc.|Needle coating formulation having lubricity and durability|

---

US10874773B2|2014-06-23|2020-12-29|Ethicon, Inc.|Two-step batch process for coating surgical needles|

---

US11197666B2|2017-09-15|2021-12-14|Cilag Gmbh International|Surgical coated needles|US9221075B2|2009-11-09|2015-12-29|Ethicon, Inc.|Surgical needle coatings and methods|

---

US9259219B2|2009-11-09|2016-02-16|Ethicon, Llc|Surgical needle coatings and methods|

---

US9332982B2|2009-11-09|2016-05-10|Ethicon, Llc|Surgical needle coatings and methods|

---

US20120321776A1|2011-06-17|2012-12-20|Robert Vetrecin|Process for in situ plasma polymerization of silicone coatings for surgical needles|

---

US9434857B2|2011-11-15|2016-09-06|Ethicon, Inc.|Rapid cure silicone lubricious coatings|

---

US8883245B2|2013-03-13|2014-11-11|Ethicon, Inc.|Method of coating surgical needles|

---

USD888954S1|2014-06-02|2020-06-30|Agnes Medical Co., Ltd.|Surgery needle for skin treatment device|

---

CN104745272B|2015-01-30|2019-08-06|宁波捷碧医疗科技有限公司|A kind of medical instrument lubricant system and its application method|

---

EP3318614B1|2015-07-01|2020-02-19|Terumo Kabushiki Kaisha|Coating agent and medical instrument surface treated with coating agent|

---

CN105268061A|2015-10-10|2016-01-27|江苏苏云医疗器材有限公司|Healing assistance injection needle tube|

---

TWI631925B|2017-03-31|2018-08-11|國立臺灣科技大學|Medical needle and method for maintaining sharpness of needle|

---

US11197666B2|2017-09-15|2021-12-14|Cilag Gmbh International|Surgical coated needles|

---

CA189341S|2018-10-29|2020-11-23|Mir Srl Medical International Res|Hand operated medical instrument|

---

USD937417S1|2019-02-22|2021-11-30|Ethicon, Inc.|Foldable suture needle|

---

USD936828S1|2019-02-22|2021-11-23|Ethicon, Inc.|Bendable suture needle|

---

USD938031S1|2019-07-14|2021-12-07|Telma Micro Needles Pvt. Ltd.|Undrilled needle|

法律状态:
2017-08-08| B25A| Requested transfer of rights approved|Owner name: ETHICON, LLC (PR) |

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2017-08-22| B25A| Requested transfer of rights approved|Owner name: ETHICON LLC (US) |

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2017-09-05| B25D| Requested change of name of applicant approved|Owner name: ETHICON LLC (US) |

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2018-04-10| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|

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2019-03-06| B06T| Formal requirements before examination [chapter 6.20 patent gazette]|

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2020-09-08| B07A| Application suspended after technical examination (opinion) [chapter 7.1 patent gazette]|

---

2021-02-17| B07A| Application suspended after technical examination (opinion) [chapter 7.1 patent gazette]|

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2021-06-01| B15K| Others concerning applications: alteration of classification|Free format text: A CLASSIFICACAO ANTERIOR ERA: C08F 8/00 Ipc: C23C 2/00 (2006.01), C09D 183/04 (2006.01), C08G 7 |

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2021-06-08| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|

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2021-08-17| B16A| Patent or certificate of addition of invention granted [chapter 16.1 patent gazette]|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 21/10/2010, OBSERVADAS AS CONDICOES LEGAIS. PATENTE CONCEDIDA CONFORME ADI 5.529/DF, QUE DETERMINA A ALTERACAO DO PRAZO DE CONCESSAO. |

优先权:

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申请号 | 申请日 | 专利标题

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US61466509A| true| 2009-11-09|2009-11-09|

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US61466909A| true| 2009-11-09|2009-11-09|

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US12/614,665|2009-11-09|

---

US12/614,669|2009-11-09|

---

US12/858,481|2010-08-18|

---

US12/858,481|US9259219B2|2009-11-09|2010-08-18|Surgical needle coatings and methods|

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PCT/US2010/053552|WO2011056453A1|2009-11-09|2010-10-21|Surgical needle coating and methods|

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