CA2015619C - Elastomeric segmented hydrophilic polyetherurethane based lubricious coatings - Google Patents
Elastomeric segmented hydrophilic polyetherurethane based lubricious coatingsInfo
- Publication number
- CA2015619C CA2015619C CA002015619A CA2015619A CA2015619C CA 2015619 C CA2015619 C CA 2015619C CA 002015619 A CA002015619 A CA 002015619A CA 2015619 A CA2015619 A CA 2015619A CA 2015619 C CA2015619 C CA 2015619C
- Authority
- CA
- Canada
- Prior art keywords
- composition
- hydrophilic
- diisocyanate
- glycol
- coating
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Classifications
-
- C—CHEMISTRY; METALLURGY
- C09—DYES; PAINTS; POLISHES; NATURAL RESINS; ADHESIVES; COMPOSITIONS NOT OTHERWISE PROVIDED FOR; APPLICATIONS OF MATERIALS NOT OTHERWISE PROVIDED FOR
- C09D—COATING COMPOSITIONS, e.g. PAINTS, VARNISHES OR LACQUERS; FILLING PASTES; CHEMICAL PAINT OR INK REMOVERS; INKS; CORRECTING FLUIDS; WOODSTAINS; PASTES OR SOLIDS FOR COLOURING OR PRINTING; USE OF MATERIALS THEREFOR
- C09D175/00—Coating compositions based on polyureas or polyurethanes; Coating compositions based on derivatives of such polymers
- C09D175/04—Polyurethanes
- C09D175/08—Polyurethanes from polyethers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
- A61L29/08—Materials for coatings
- A61L29/085—Macromolecular materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2400/00—Materials characterised by their function or physical properties
- A61L2400/10—Materials for lubricating medical devices
Landscapes
- Chemical & Material Sciences (AREA)
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- Wood Science & Technology (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Animal Behavior & Ethology (AREA)
- Epidemiology (AREA)
- Materials Engineering (AREA)
- General Health & Medical Sciences (AREA)
- Organic Chemistry (AREA)
- Materials For Medical Uses (AREA)
- Coating Of Shaped Articles Made Of Macromolecular Substances (AREA)
- Polyurethanes Or Polyureas (AREA)
- Floor Finish (AREA)
- Laminated Bodies (AREA)
- Paints Or Removers (AREA)
- Compositions Of Macromolecular Compounds (AREA)
Abstract
A coating composition for an article surface includes a uniform blend of an elastomeric segmented hydrophilic polyetherurethane and a hydrophilic polymer, such as polyvinylpyrrolidone.
The invention includes a method for rendering an article surface lubricious which includes coating the composition onto the article surface and contacting the coated surface with an aqueous liquid.
The invention includes a method for rendering an article surface lubricious which includes coating the composition onto the article surface and contacting the coated surface with an aqueous liquid.
Description
ELASTOMERIC SEGMENTED HYDROPHILIC
POLYETHERURETHANE BASED LUBRICIOUS COATINGS
BACKGROUND OF THE INVENTION
1. Field of the Invention. This invention relates to lubricated surfaces. More particularly, the invention relates to a coating for a surface which is lubricious and biocompatible when in contact with a body fluid, and to a method for preparing same.
POLYETHERURETHANE BASED LUBRICIOUS COATINGS
BACKGROUND OF THE INVENTION
1. Field of the Invention. This invention relates to lubricated surfaces. More particularly, the invention relates to a coating for a surface which is lubricious and biocompatible when in contact with a body fluid, and to a method for preparing same.
2. Backqround. Many articles, devices and products require a lubricated surface. In the medical instrumentation and diagnostic field, simple sensing devices such as, for example, thermometers and needles, or electrode components of complex monitoring apparatuses, must be inserted into a body cavity or through the skin and at a later time withdrawn. Patient treatment often includes catheterization procedures or nutrition delivery systems, most of which involve invasive techniques.
In all such cases, effective lubrication which is stable throughout both the insertion and withdrawal stages of the procedure contributes greatly to patient comfort.
Many medical devices are fabricated from glass or polymeric materials such as polypropylene, polyvinyl chloride, polytetrafluoroethylene and polyurethane. Such materials are for the most part inherently nonlubricious. A variety of approaches to introduce lubricity have been advanced. Simple coatings of lubricants such as mineral oils or silicones to glass or polymeric surfaces are Zt~15619 generally unsatisfactory because the surface energy is too low and the lubricant tends to migrate or "bead." A method to overcome migration of silicone lubricants is described by Williams et al. in U.S.
Patent No. 4,767,414. A surface to be lubricated is coated with silicone oil and both the surface and oil are subjected to an ionizing plasma.
Spielvogel et al., in U.S. Patent No. 4,720,521 teaches adherence of a lubricating composition to a surface. The composition includes a polysiloxane lubricant entrapped in a mixture of a plurality of reactive silicone components which, on curing, adhere to the surface.
Thermoplastic polyurethanes prepared from polyisocyanates, high molecular weight polyether-glycols, and low molecular weight diols and diamines as chain extenders are conventionally referred to as polyetherurethanes, and this term, will be used in this disclosure for polyurethanes having a polyether backbone.
Polyetherurethane compositions develop microdomains conventionally termed hard segment domains and soft segment domains and are often referred to as segmented polyurethanes. They are (AB)n type block copolymers, A being the hard segment and B the soft segment. The hard segment domains form by localization of the portions of the copolymer molecules which include the isocyanate and extender components whereas the soft segment domains form from the polyether glycol portions of the copolymer chains. The phase seperated microdomain 2~
In all such cases, effective lubrication which is stable throughout both the insertion and withdrawal stages of the procedure contributes greatly to patient comfort.
Many medical devices are fabricated from glass or polymeric materials such as polypropylene, polyvinyl chloride, polytetrafluoroethylene and polyurethane. Such materials are for the most part inherently nonlubricious. A variety of approaches to introduce lubricity have been advanced. Simple coatings of lubricants such as mineral oils or silicones to glass or polymeric surfaces are Zt~15619 generally unsatisfactory because the surface energy is too low and the lubricant tends to migrate or "bead." A method to overcome migration of silicone lubricants is described by Williams et al. in U.S.
Patent No. 4,767,414. A surface to be lubricated is coated with silicone oil and both the surface and oil are subjected to an ionizing plasma.
Spielvogel et al., in U.S. Patent No. 4,720,521 teaches adherence of a lubricating composition to a surface. The composition includes a polysiloxane lubricant entrapped in a mixture of a plurality of reactive silicone components which, on curing, adhere to the surface.
Thermoplastic polyurethanes prepared from polyisocyanates, high molecular weight polyether-glycols, and low molecular weight diols and diamines as chain extenders are conventionally referred to as polyetherurethanes, and this term, will be used in this disclosure for polyurethanes having a polyether backbone.
Polyetherurethane compositions develop microdomains conventionally termed hard segment domains and soft segment domains and are often referred to as segmented polyurethanes. They are (AB)n type block copolymers, A being the hard segment and B the soft segment. The hard segment domains form by localization of the portions of the copolymer molecules which include the isocyanate and extender components whereas the soft segment domains form from the polyether glycol portions of the copolymer chains. The phase seperated microdomain 2~
structure forms if the hard segments of polyetherurethane chain are a certain size. A long hard segment promotes the phase separated microdomain structure. Conversely, non-extended formulations (those lacking an extender) have very short hard segments and minimum phase seperated microdomain structure. The hard segment is crystalline and provides physical crosslinking and reinforcement. The polyether glycol soft segment is mostly in a rubbery state and provides elasticity.
Therefore, polyetherurethanes are thermoplastic elastomeric materials. A wide range of physical properties can be obtained by altering the relative ratios of the hard and soft segments. The elasticity, toughness and other desirable properties of polyetherurethanes are the result of their phase seperated microdomain structure.
Elastomeric segmented polyurethanes have particular advantages for fabrication of medical devices, as discussed by Gilding et al. in U.S.
Patent No. 4,062,834 but have limited inherent lubricity. Micklus et al. in U.S. Patent No.
Therefore, polyetherurethanes are thermoplastic elastomeric materials. A wide range of physical properties can be obtained by altering the relative ratios of the hard and soft segments. The elasticity, toughness and other desirable properties of polyetherurethanes are the result of their phase seperated microdomain structure.
Elastomeric segmented polyurethanes have particular advantages for fabrication of medical devices, as discussed by Gilding et al. in U.S.
Patent No. 4,062,834 but have limited inherent lubricity. Micklus et al. in U.S. Patent No.
4,100,309 teaches a lubricious polyurethane-poly-vinylpyrrolidone (PVP) interpolymer coating which may be applied to a polymeric article by dipping the article into a solvent solution of polyurethane and a polyisocyanate to give an isocyanate-containing prepolymer on the article surface and dipping the prepolymer-coated article into a solution of PVP.
In U.S. Patent No. 4,373,009 to Winn, a substrate surface is primed with a polyisocyanate as 20156~9 shown by Micklus et al., and the isocyanate groups are covalently bonded to active hydrogens of a hydrophilic copolymer, such as a copolymer of PVP
and acrylamide. A coating which is stable and resistant to removal, in contrast to prior art coating, is claimed.
U.S. Patent No. 4,642,267 to Creasy et al.
describes lubricious coatings which are alloys or blends of PVP and polyurethanes lacking both free isocyanate groups and chain extenders.
Although the above disclosures have advanced the art of rendering surfaces lubricious, there remains a need for a coating which is instantly lubricious, easily applied and strongly adherent so as to remain on the substrate to which it is applied with no tendency to wash off or separate as solid flakes on prolonged contact with liquids.
SUMMARY OF THE INVENTION
One aspect of the present invention is a coating composition for articles which includes a uniform blend of a hydrophilic polymer and an elastomeric segmented hydrophilic polyetherurethane (HPEU). Preferred compositions are blends of PVP
and a diol extended HPEU which includes polyethyleneoxide as the soft segment. The most preferred composition has a hard segment content of about 35 to 45%.
Another aspect of the invention is a method to render the surface of an article lubricious by 2nls6l.~
p-1488 coating the surface with the composition of the invention. Preferably, the article is dipped into a solution of the composition in an appropriate solvent and the solution then evaporated. The article thus coated with the composition is brought into contact with a liquid, preferably an aqueous liquid, whereby the article surface is rendered lubricious. Most preferably, a medical device, such as a catheter, is coated with the composition.
In accordance with the invention, the surface of a medical article is rendered instantly lubricious when coated with the composition and wetted with an aqueous liquid or water. The composition adheres firmly to the surface of the article through the HPEU component. The PVP
component is trapped in the HPEU matrix as a result of strong hydrogen bonding and migrates slowly to the surface of the HPEU when the composition is in contact with the liquid. The mobile PVP on the surface is believed to account for the outstanding lubricity of articles coated with the composition.
Because the migration is slow, the article remains lubricious for prolonged times.
In particular, the inclusion of the elastomeric segmented HPEU provides hard segments through which exceptionally strong hydrogen bonding to the article surface are formed so that there is no tendency for the coating to separate from the surface, even under conditions of exposure to flowing liquids, as blood. Further, the elastomeric segmented HPEU
having phase separated microstructure contributes to a surface having a high level of biocompatibility, ~nls~ls in particular excellent blood compatibility and thus very low thrombogenicity and very low toxicity.
DETAILED DESCRIPTION
While this invention is satisfied by embodiments in many different forms, there will herein be described in detail preferred embodiments of the invention, with the understanding that the present disclosure is to be considered as exemplary of the principles of the invention and is not intended to limit the invention to the embodiments described. The scope of the invention will be measured by the appended claims and their equivalents.
In this disclosure the following abbreviations are used:
PEG polyethyleneoxide glycol PU polyurethane PEU polyetherurethane PVP polyvinylpyrrolidone HPEU hydrophilic polyetherurethane PVC polyvinyl chloride MDI 4,4'-diphenylmethane diisocyanate PEO polyethyleneoxide (molecular weight of 100,000 or higher) BDO 1,4-butanediol DMF dimethylformamide DMAC dimethylacetamide NMP N-methylpyrrolidone MEK methyl ethyl ketone THF tetrahydrofuran 2! )lS6~ 9 DEA diethyl ethanolamine TEA triethylamine DAA diacetone alcohol NEPEU nonextended polyetherurethane NEHPEU non extended hydrophilic polyether-urethane HS hard segment In accordance with the present invention, it has been found that HPEUs have many salubrious properties which make them attractive as base materials in lubricious coatings. Particularly useful are elastomeric segmented HPEUs which adhere well to a variety of substrates and provide exceptional properties not shown by linear, non-extended PUs.
The hard segment-soft segment ratio greatly influences the properties of a HPEU and may be varied over a wide range by varying the proportions of the polyisocyanate, polyetherglycol and extender included in the formulation. HPEUs of low hard segment content are generally soft, of low mechanical strength and absorb water to such an extent that they are poorly adherent when coated on most polymeric substrates. On the other hand, HPEUs of high hard segment content have a high degree of crystallinity and are strongly adherent to polymeric substrates but the pronounced phase separation reduces the ability of the base HPEU to blend well with lubricious components.
The present invention provides a method for znls6l9 coating a polymeric substrate with a composition which gives a stable lubricious substrate surface when the substrate comes into contact with a liquid. The composition of the invention includes an elastomeric segmented HPEU and a hydrophilic polymer.
A variety of substrates is contemplated to be coated with the PU composition of the invention.
The substrate may, for example, be glass, metal such as steel, or preferably a polymer. Preferred polymeric substrates are polytetrafluoroethylene, polyester, polyamide, PVC, polyacrylate, polystyrene, latex rubber and, most preferably PU.
Most preferably, a PVC or PU substrate is shaped into the form of a desired medical article, such as a catheter tubing, and the composition of the invention coated onto the shaped article.
HPEUs suitable for use as the base component of the coating composition of present invention include three essential components, a diisocyanate, a polyether glycol and a chain extender. Suitable diisocyanates are aromatic diisocyanates such as MDI, alicyclic diisocyanates such as isophorone diisocyanate and 4,4'-dicyclohexylmethane diisocyanate, and aliphatic diisocyanates, as, for example, hexamethylene diisocyanate. The most preferred diisocyanate is MDI.
The polyether glycol component may be PEG, alone or mixed with polypropyleneoxide glycol or 3D polytetramethyleneoxide glycol. The preferred polyol is PEG having a molecular weight of from 2015~
_ g _ about 600 to 3300, or a mixture containing 50% or more by weight thereof. The most preferred polyether glycol is a PEG having an average molecular weight of 1000 to 1450.
The chain extender may be water and/or a low molecular weight branched or unbranched diol, diamine or aminoalcohol of up to 10 carbon atoms or mixtures thereof. Representative nonlimiting examples of chain extenders are BDO; ethylene glycol; diethylene glycol; triethylene glycol;
1,2-propanediol; 1,3-propanediol; 1,6-hexanediol;
1,4-bis-hydroxymethyl cyclohexane, hydroquinone dihydroxyethyl ether, ethanolamine, ethylenediamine and hexamethylenediamine. Preferred chain extenders are 1,6-hexanediol, ethylenediamine hexamethylene-diamine and, most preferably, BDO.
The percentages of the components may be such that the hard and soft segments of the composition may be from about 25 to 60 and from about 40 to 75, preferably from about 30 to 50% and 50 to 70%
respectively of the total weight of the formulation. From these percentages and ratios, suitable proportions of the components may readily be calculated. Representative elastomeric segmented HPEU base components are listed in Table I of Example I below.
The HPEU base component of the composition maybe prepared by solution or bulk synthesis methods.
Example I provides typical procedures, however, various modifications of this conventional procedure are well-known to those skilled in the art.
2n~s Alternatively, the HPEU may be prepared by conventional emulsion polymerization, in water, to give an HPEU latex.
A feature of the method for preparing the HPEU
formulations of the invention is that the polymers are prepared from the components without adding a polymerization catalyst. Conventional catalysts in the art, for example, organometallic compounds such as dibutyl tin dilaurate, are leachable and may cause deleterious effects in blood-contacting elements fabricated from prior art catalyst-containing HPEU. By avoiding use of a catalyst, HPEUs of the invention are purer and potentially less toxic than those of the prior art.
A second component of the coating composition of the present invention is a water soluble hydrophilic polymer. Exemplary of suitable hydrophilic polymers are polyacrylic acid, polyvinyl pyridine, polyvinylmethyl ether, polyhydroxyethyl methacrylate, PEO and, preferably PVP. While the PVP of the invention may be of any suitable molecular weight, it is preferred to use a PVP
having a molecular weight of about 10,000 to 1,000,000.
The coating composition of the present invention may be prepared by mixing the HPEU and PVP
components in a suitable solvent wherein the ratio of HPEU to PVP may be from about 25 to 0.05, preferably about 4 to 0.25 parts by weight. In the most preferred composition, 1 part of HPEU and 1 part of PVP are mixed. Suitable solvents are DMAC, ~i~6:~
DMF, and the composition may be about 1 to 20, preferably about 4 to 12% by weight in the solvent.
The composition dissolved in the solvent may be applied to the substrate surface by any suitable method such as brushing, spraying or, preferably continuous dip coating. The substrate may be dipped into the solvent solution of the composition at any suitable temperature up to the boiling point of the solvent. The dipping procedure may preferably be carried out at ambient temperature for a time of 1 sec. up to 30 minutes. Dipping is preferably carried out for about 1 to 30 seconds. After the dipping process is complete, the solvent may be removed, under forced evaporation at ambient temperature, preferably by warming the coated substrate in an oven at about 50~C to 200~C.
Depending on the intended use, other components may be incorporated into the coating composition of the invention in order to achieve particular properties. For example additives such as flow aids, flatting agents, plasticizers, heat stabilizers and surface cure modifiers may be added to the formulation prior to prepolymer formation, prior to conversion of the prepolymer to the HPEU, or preferably directly to the solvent solution of the components prior to coating. Such additives and their use to modify polymer properties are conventional and well known to those skilled in the art.
Particularly preferred is addition of an antimicrobial agent to the coating composition. Any 2nls~l~
antimicrobial agent which is substantially stable and which may be released slowly from the coating may be used. Exemplary of suitable antimicrobial agents are povidone iodine, chlorohexidene or chlorohexidene iodine complex. The quantity of antimicrobial agent to be added may be from about 1 to 10, preferably 2 to 6 weight percent.
The substrate coated with the composition of the invention is dry and nonsticky to the touch until wet with a liquid, at which time it develops a slippery lubricious feel. It is believed, although as yet unsubstantiated, that the preferred coating of the invention includes strong hydrogen bonding between the HPEU and PVP chains so that the chains of PVP are substantially trapped in the HPEU base polymer without actually being chemically linked thereto. This arrangement of the two polymers provides the coating with the mechanical strength and bonding capability of segmented PUs yet leaves the PVP molecules unattached so that slow diffusion of the hydrophilic polymer to the surface of the coated substrate may take place.
The coating composition of the invention is particularly useful when applied to medical devices. For example, a catheter coated with the composition becomes instantly lubricious when it comes into contact with water or a body fluid such as blood and thereby contributes greatly to the comfort of a patient undergoing catheterization.
One skilled in the art will immediately recognize other medical devices, such as nutrition delivery systems, cannulas, needles, thermometers, urethral 2015~
catheters and various components of medical monitoring apparatuses which may advantageously be coated with the composition of the invention.
Representative coating compositions of the invention are listed in Table II of Example II. The coatings of the invention were applied to a polymeric substrate by the procedure of Example III
and tested for stability as described in Example IV
and were found to be substantially more stable than coatings prepared from prior art PUs, Substrates coated with the composition of the invention are substantially dry until contacted with a liquid whereupon they are instantly rendered lubricious. Lubricity of the coated surfaces were determined by measuring their coefficients of friction using the Instron Model 1122 Universal Testing Machine by the procedure described in Example V. Lubricity data is given in Table II
which accompanies Example II.
The following examples are given to further illustrate the invention but are not to be considered as limitative thereof.
EXAMPLE I
Bulk Synthesis PEG was dried at 60 to 70~C under vacuum (4-6 mm Hg) for 4 to 6 hours to remove moisture. Water content (Carl Fisher titration) and polyol hydroxyl number ~phthalic anhydride-pyridine method) were determined to adjust formulation stoichiometry. MDI
was filtered to remove any reacted diisocyanate and vacuum stripped (4-6 mm Hg) for 2 to 4 hours. The stoichimetric amounts of PEG and BDO were placed in the polymerization vessel and degassed at 60~ for 30 minutes. Then, the stoichiometric amount of MDI
(1.02 index) was added and the mixture stirred vigorously until the polymerization temperature reached about 85 to 90~C. The polymer was discharged and postcured at 125~C for 30 minutes.
Solution Synthesis Solution polymerization at 25~ total solids was performed in DMAC under a nitrogen atmosphere. PEG
was dried at 60 to 70~C under vacuum (4-6 mm Hg) for 4 to 6 hours to remove moisture. Water content (Carl Fisher titration) and polyol hydroxyl number (phthalic anhydride-pyridine method) were determined to adjust formulation stoichiometry. MDI was filtered to remove any reacted diisocyanate and vacuum stripped (4-6 mm Hg) for 2 to 4 hours.
Stoichiometric amounts of PEG and BDO were placed in the polymerization vessel and degassed at 60~C for 30 minutes. Two thirds of the total solvent used (DMAC) was added to the PEG-extender mixture. The stoichiometric (1.02 Index) amount of MDI was dissolved in the remaining DMAC and the solution was added dropwise to the polymerization vessel. The polymerization medium was maintained at 60 to 70~C
and constantly stirred. A polymerization time of four hours at 60 to 70~C was sufficient for adequate formation.
Z~)~561~
TABLE I
Typical HPEUs of the Invention HPEU HS CONTENTPOLYETHER NUMBER OF EQUIVALENTS OF
NO. (% WT) TYPE MDI BDO PEG
1 30 PEG 14501.02 0.506 0.494 2 35 PEG 14501.02 0.597 0.403 3 40 PEG 14501.02 0.667 0.333 4 45 PEG 14501.02 0.738 0.262 PEG 14501.02 0.772 0.228 6 55 PEG 14501.02 0.821 0.179 7 60 PEG 14501.02 0.845 0.155 E~MPLE II
Preparation of Lubricious Coatinq The HPEU of Example I was dissolved in DMF and the desired amount of PVP (K-90, Aldrich) was added. The solution concentration and the solvent ratio of the lubricious coating solution were adjusted by adding THF.
znlS61~
TABLE II
Examples of HPEU Based Lubricious Coating Compositions of the Invention COMPOSITION ~PEU ~PEU/PVP CONC~UTP~TTON SOLV~NTS & COEFFICIENI*
NO. HS~ RATIO(~ SOLID) RATIOSOF FRICTION
1 40 3~7 6 DffF/T~F (3/2) 0.114 + 0.006 2 40 1/1 6 "0.118 + 0.013 3 40 3/7 10 "0.107 + 0.004 4 40 1/1 10 "0.130 + 0.004 0 5 50 3/7 6 "0.108 + 0.012 6 50 3/7 10 0.067 + 0.007 7 50 1/1 10 "0.121 + 0.003 8 60 3/7 6 "0.094 + 0.003 9 60 3/~ 10 "0.085 + 0.003 1 5 10 60 1/1 10 "0.114 + 0.004 PVC CONTXOL (UNCOATED FXOSTED PVC TUBrNG) 0.986 + 0.048 * Detern~d br the pLoeed~,~ of EYample V.
EXAMPLE III
Coating Application Procedure The lubricious coatings of this invention were applied to PVC tubing by dip coating. Tubing samples were cut to desired lengths and were heat sealed at one end to contain the coating application to the outer surface only. The thickness of the 2 5 applied coating was adjusted by changing the dipping rate and the coating solution concentration. The tubing samples were vertically dipped into the 2~156~
coating solutions of Table II (6-10~ solids). The coated samples were first placed in a convection oven at 125~C for 30 seconds, then transferred to another convection oven at 65~C for 30 to 45 minutes to remove the solvents.
EXAMPLE IV
Lubricious Coating Stability Test The following tests were employed for determining the stability of the lubricious coatings;
1. The coated tubing samples were placed in distilled water for a few minutes (2 to 5 minutes) and examined visually for signs of delamination. No lubricity testing was performed on samples that delaminated; they were considered unstable.
2. The lubricious coatings that passed the first test were evaluated in the lubricity test.
Samples that delaminated during the lubricity test were also considered unstable.
3. Samples that withstood tests 1 and 2, were then tested for the coating adhesion strength as follows: samples were placed in distilled water and vigorously stirred at room temperature for one hour. Samples were visually inspected for lubricious coating delamination.
4. Finally, samples were stored in distilled water at room temperature for 1 to 5 days, then 2nls6i ~
- tested for forced delamination by subjecting to the lubricity test. Samples were examined for signs of delamination during the lubricity test.
The lubricious coating stability of the samples that successfully passed test 1 to 4 was rated as excellent. The lubricious coating stability of the samples that failed at any of these four tests were considered unstable.
EXAMPLE V
loLubricity Testinq The lubricity of the disclosed formulations were evaluated by comparing the surface coefficients of friction of the coated samples with that of the uncoated substrate. Surface coefficients of friction were determined using an Instron Universal Testing Machine, Model 1122, and the drag generated between the sample and a natural rubber substrate was measured. Test samples were secured in a water filled trough and were soaked for 5 minutes before testing. A piece of clean natural pure gum rubber (lab grade, Fisher Scientific) was placed in contact with the test sample under water and pulled at a constant speed (5 cm/min) under a standard applied load (532 gm). The measured drag force in newtons (N) was converted--to the coefficient of friction (CF) using the following equation:
Drag Force (N) - Internal Friction (N) CF =
0.0098 (N/gm) x Applied Load (gm) ~n~
where the internal friction is the drag generated by the friction apparatus in the absence of sample contact.
EXAMPLE VI
Preparation of Prior Art Coatings and Comparative Study with Coatinqs of the Invention A. NEPEU Synthesis:
Polytetramethyleneoxide glycol of 1000 molecular weight, (Terathane 1000, DuPont), was dried at 60 to 70~C under vacuum (4 to 6 mm Hg) for 4 to 6 hours to remove moisture. MDI was filtered to remove any reacted diisocyanate and vacuum stripped (4 to 6 mm Hg) for 2 to 4 hours. Polyol was weighed and placed in the polymerization vessel. Then the weighed amount of MDI (30%, 40%, 50% by weight) was added, and the mixture stirred vigorously for 15 minutes. The NEPEU thus obtained was stored under nitrogen in a tightly closed jar.
B. NEHPEU Synthesis: ~
PEG of 1450 molecular weight (Union Carbide) was dried at 60 to 70~C under vacuum (4 to 6 mm Hg) for 4 to 6 hours to remove moisture. MDI was filtered to remove any reacted diisocyanate and vacuum stripped (4 to 6 mm Hg) for 2 to 4 hours.
The PEG was weighed and placed in the polymerization vessel, the weighed amount of MDI (40%, 50% by weight) was added, and the mixture stirred ~201'5~
-vigorously for 15 minutes. The NEHPEU thus obtained was stored under nitrogen in a tightly closed jar.
C. NEPEU and NEHPEU based lubricious coatinq preparation:
The NEPEU and NEHPEU PUs from A and B were dissolved in DMF or DMAC. To this solution a desired amount of PVP (K-90, Aldrich) was added, and the polymer contents were dissolved by constant shaking. The solution concentration and the solvent ratio of the lubricious coating solution were adjusted by adding THF or MEK. The coatings were applied to PVC tubing as described in Example III
for stability and lubricity tests.
D. ESTANE 5703 based lubricious coatinq preparation and application:
To a mixture of 75 gm of DAA and 25 gm of MEK
were added 4 gm of PVP (K-90, Aldrich) and 2 gm of linear PU (Estane*5703, B.F. Goodrich). The polymer contents were dissolved by constant shaking. The resulting coating solution was applied to PVC tubing using the standard coating application procedure.
E. NEOREZ R940 based lubricious coatinq preparation and application:
To 47 gm of water and 10 gm of NMP were added 10 gm of PVP (K-90, Aldrich) and 33 gm of linear PU
aqueous dispersion (Neorez R940, ICI, formerly Polyvinyl Chemical Industries). The polymer contents were dissolved by constant shaking. The ~ ~a 1~5 ~ ~ ~
resulting solution was applied to PVC tubing using the standard coating application procedure.
The coatings the prior art described in A-E and applied to PVC tubing are listed in Table III as compositions 7-13 and may -be compared with compositions 1-6 of the invention. --TA~LEIII
COMPARATIVE LUBRIC-OUS COAnNG COMPOSmONS
COMPOSITION PU/PVP SOL. CONC SOLVENr'S ADHESION COEFFlClENT
NO. PU RATIO (% SOLID) AND RAnOS STABILIl-Y OF FRICllON
- I HPEU 40% HS 3/7 6 DMF/THF (3/Z E~cellent 0.114 + 0.006 2 HPEU409o HS 1/1 6 DMF/THF(3/t E~cellent 0.118 + 0.013 3 HPEU 409rC HS 3/7 10 DMF~THF (3/21 E~cellent Q107 + 0.004 4 HPEU S096 HS 3/7 6 DMFrlHF (3n,~ E~cellent 0.108 + Q012 S HPEU S0~o HS 1/1 10 DMF/THF (3/2) E~cellent 0.121 + Q003 6 HPEU 50% HS 3/7 10 DMF/THF(3/Z) E~cellent Q067 + 0.007 7 ESTANE S703 In S.7 DAA/MEK (3/1) Unstable N/A--8 NEOREZ R940 1/1 22 ~ Unstable N/A
9 NEPEU-30 1/1 6 DMAC/MEK (3/2) Unstable. N/A
NEPEU40 1/1 6 DMAC/MEK (3n) Ulutable N/A
NEPEU-S0 1/1 6 DMACMEK (3/2) U~able N/A
12 NEHPEU-40 1/1 6 DMF/'IHF (3n) Unstable N/A
13 NEHPEU-50 1/1 6 DMF/THF (3n) Unstable N/A
~wATER~NMp~MEJcfDE~ + 'IE~ t~l 3 6/~ 6~n ~-Not ~ bk ~ 8 ~ ' - ' durulB tes~ing in ~ pk V
In U.S. Patent No. 4,373,009 to Winn, a substrate surface is primed with a polyisocyanate as 20156~9 shown by Micklus et al., and the isocyanate groups are covalently bonded to active hydrogens of a hydrophilic copolymer, such as a copolymer of PVP
and acrylamide. A coating which is stable and resistant to removal, in contrast to prior art coating, is claimed.
U.S. Patent No. 4,642,267 to Creasy et al.
describes lubricious coatings which are alloys or blends of PVP and polyurethanes lacking both free isocyanate groups and chain extenders.
Although the above disclosures have advanced the art of rendering surfaces lubricious, there remains a need for a coating which is instantly lubricious, easily applied and strongly adherent so as to remain on the substrate to which it is applied with no tendency to wash off or separate as solid flakes on prolonged contact with liquids.
SUMMARY OF THE INVENTION
One aspect of the present invention is a coating composition for articles which includes a uniform blend of a hydrophilic polymer and an elastomeric segmented hydrophilic polyetherurethane (HPEU). Preferred compositions are blends of PVP
and a diol extended HPEU which includes polyethyleneoxide as the soft segment. The most preferred composition has a hard segment content of about 35 to 45%.
Another aspect of the invention is a method to render the surface of an article lubricious by 2nls6l.~
p-1488 coating the surface with the composition of the invention. Preferably, the article is dipped into a solution of the composition in an appropriate solvent and the solution then evaporated. The article thus coated with the composition is brought into contact with a liquid, preferably an aqueous liquid, whereby the article surface is rendered lubricious. Most preferably, a medical device, such as a catheter, is coated with the composition.
In accordance with the invention, the surface of a medical article is rendered instantly lubricious when coated with the composition and wetted with an aqueous liquid or water. The composition adheres firmly to the surface of the article through the HPEU component. The PVP
component is trapped in the HPEU matrix as a result of strong hydrogen bonding and migrates slowly to the surface of the HPEU when the composition is in contact with the liquid. The mobile PVP on the surface is believed to account for the outstanding lubricity of articles coated with the composition.
Because the migration is slow, the article remains lubricious for prolonged times.
In particular, the inclusion of the elastomeric segmented HPEU provides hard segments through which exceptionally strong hydrogen bonding to the article surface are formed so that there is no tendency for the coating to separate from the surface, even under conditions of exposure to flowing liquids, as blood. Further, the elastomeric segmented HPEU
having phase separated microstructure contributes to a surface having a high level of biocompatibility, ~nls~ls in particular excellent blood compatibility and thus very low thrombogenicity and very low toxicity.
DETAILED DESCRIPTION
While this invention is satisfied by embodiments in many different forms, there will herein be described in detail preferred embodiments of the invention, with the understanding that the present disclosure is to be considered as exemplary of the principles of the invention and is not intended to limit the invention to the embodiments described. The scope of the invention will be measured by the appended claims and their equivalents.
In this disclosure the following abbreviations are used:
PEG polyethyleneoxide glycol PU polyurethane PEU polyetherurethane PVP polyvinylpyrrolidone HPEU hydrophilic polyetherurethane PVC polyvinyl chloride MDI 4,4'-diphenylmethane diisocyanate PEO polyethyleneoxide (molecular weight of 100,000 or higher) BDO 1,4-butanediol DMF dimethylformamide DMAC dimethylacetamide NMP N-methylpyrrolidone MEK methyl ethyl ketone THF tetrahydrofuran 2! )lS6~ 9 DEA diethyl ethanolamine TEA triethylamine DAA diacetone alcohol NEPEU nonextended polyetherurethane NEHPEU non extended hydrophilic polyether-urethane HS hard segment In accordance with the present invention, it has been found that HPEUs have many salubrious properties which make them attractive as base materials in lubricious coatings. Particularly useful are elastomeric segmented HPEUs which adhere well to a variety of substrates and provide exceptional properties not shown by linear, non-extended PUs.
The hard segment-soft segment ratio greatly influences the properties of a HPEU and may be varied over a wide range by varying the proportions of the polyisocyanate, polyetherglycol and extender included in the formulation. HPEUs of low hard segment content are generally soft, of low mechanical strength and absorb water to such an extent that they are poorly adherent when coated on most polymeric substrates. On the other hand, HPEUs of high hard segment content have a high degree of crystallinity and are strongly adherent to polymeric substrates but the pronounced phase separation reduces the ability of the base HPEU to blend well with lubricious components.
The present invention provides a method for znls6l9 coating a polymeric substrate with a composition which gives a stable lubricious substrate surface when the substrate comes into contact with a liquid. The composition of the invention includes an elastomeric segmented HPEU and a hydrophilic polymer.
A variety of substrates is contemplated to be coated with the PU composition of the invention.
The substrate may, for example, be glass, metal such as steel, or preferably a polymer. Preferred polymeric substrates are polytetrafluoroethylene, polyester, polyamide, PVC, polyacrylate, polystyrene, latex rubber and, most preferably PU.
Most preferably, a PVC or PU substrate is shaped into the form of a desired medical article, such as a catheter tubing, and the composition of the invention coated onto the shaped article.
HPEUs suitable for use as the base component of the coating composition of present invention include three essential components, a diisocyanate, a polyether glycol and a chain extender. Suitable diisocyanates are aromatic diisocyanates such as MDI, alicyclic diisocyanates such as isophorone diisocyanate and 4,4'-dicyclohexylmethane diisocyanate, and aliphatic diisocyanates, as, for example, hexamethylene diisocyanate. The most preferred diisocyanate is MDI.
The polyether glycol component may be PEG, alone or mixed with polypropyleneoxide glycol or 3D polytetramethyleneoxide glycol. The preferred polyol is PEG having a molecular weight of from 2015~
_ g _ about 600 to 3300, or a mixture containing 50% or more by weight thereof. The most preferred polyether glycol is a PEG having an average molecular weight of 1000 to 1450.
The chain extender may be water and/or a low molecular weight branched or unbranched diol, diamine or aminoalcohol of up to 10 carbon atoms or mixtures thereof. Representative nonlimiting examples of chain extenders are BDO; ethylene glycol; diethylene glycol; triethylene glycol;
1,2-propanediol; 1,3-propanediol; 1,6-hexanediol;
1,4-bis-hydroxymethyl cyclohexane, hydroquinone dihydroxyethyl ether, ethanolamine, ethylenediamine and hexamethylenediamine. Preferred chain extenders are 1,6-hexanediol, ethylenediamine hexamethylene-diamine and, most preferably, BDO.
The percentages of the components may be such that the hard and soft segments of the composition may be from about 25 to 60 and from about 40 to 75, preferably from about 30 to 50% and 50 to 70%
respectively of the total weight of the formulation. From these percentages and ratios, suitable proportions of the components may readily be calculated. Representative elastomeric segmented HPEU base components are listed in Table I of Example I below.
The HPEU base component of the composition maybe prepared by solution or bulk synthesis methods.
Example I provides typical procedures, however, various modifications of this conventional procedure are well-known to those skilled in the art.
2n~s Alternatively, the HPEU may be prepared by conventional emulsion polymerization, in water, to give an HPEU latex.
A feature of the method for preparing the HPEU
formulations of the invention is that the polymers are prepared from the components without adding a polymerization catalyst. Conventional catalysts in the art, for example, organometallic compounds such as dibutyl tin dilaurate, are leachable and may cause deleterious effects in blood-contacting elements fabricated from prior art catalyst-containing HPEU. By avoiding use of a catalyst, HPEUs of the invention are purer and potentially less toxic than those of the prior art.
A second component of the coating composition of the present invention is a water soluble hydrophilic polymer. Exemplary of suitable hydrophilic polymers are polyacrylic acid, polyvinyl pyridine, polyvinylmethyl ether, polyhydroxyethyl methacrylate, PEO and, preferably PVP. While the PVP of the invention may be of any suitable molecular weight, it is preferred to use a PVP
having a molecular weight of about 10,000 to 1,000,000.
The coating composition of the present invention may be prepared by mixing the HPEU and PVP
components in a suitable solvent wherein the ratio of HPEU to PVP may be from about 25 to 0.05, preferably about 4 to 0.25 parts by weight. In the most preferred composition, 1 part of HPEU and 1 part of PVP are mixed. Suitable solvents are DMAC, ~i~6:~
DMF, and the composition may be about 1 to 20, preferably about 4 to 12% by weight in the solvent.
The composition dissolved in the solvent may be applied to the substrate surface by any suitable method such as brushing, spraying or, preferably continuous dip coating. The substrate may be dipped into the solvent solution of the composition at any suitable temperature up to the boiling point of the solvent. The dipping procedure may preferably be carried out at ambient temperature for a time of 1 sec. up to 30 minutes. Dipping is preferably carried out for about 1 to 30 seconds. After the dipping process is complete, the solvent may be removed, under forced evaporation at ambient temperature, preferably by warming the coated substrate in an oven at about 50~C to 200~C.
Depending on the intended use, other components may be incorporated into the coating composition of the invention in order to achieve particular properties. For example additives such as flow aids, flatting agents, plasticizers, heat stabilizers and surface cure modifiers may be added to the formulation prior to prepolymer formation, prior to conversion of the prepolymer to the HPEU, or preferably directly to the solvent solution of the components prior to coating. Such additives and their use to modify polymer properties are conventional and well known to those skilled in the art.
Particularly preferred is addition of an antimicrobial agent to the coating composition. Any 2nls~l~
antimicrobial agent which is substantially stable and which may be released slowly from the coating may be used. Exemplary of suitable antimicrobial agents are povidone iodine, chlorohexidene or chlorohexidene iodine complex. The quantity of antimicrobial agent to be added may be from about 1 to 10, preferably 2 to 6 weight percent.
The substrate coated with the composition of the invention is dry and nonsticky to the touch until wet with a liquid, at which time it develops a slippery lubricious feel. It is believed, although as yet unsubstantiated, that the preferred coating of the invention includes strong hydrogen bonding between the HPEU and PVP chains so that the chains of PVP are substantially trapped in the HPEU base polymer without actually being chemically linked thereto. This arrangement of the two polymers provides the coating with the mechanical strength and bonding capability of segmented PUs yet leaves the PVP molecules unattached so that slow diffusion of the hydrophilic polymer to the surface of the coated substrate may take place.
The coating composition of the invention is particularly useful when applied to medical devices. For example, a catheter coated with the composition becomes instantly lubricious when it comes into contact with water or a body fluid such as blood and thereby contributes greatly to the comfort of a patient undergoing catheterization.
One skilled in the art will immediately recognize other medical devices, such as nutrition delivery systems, cannulas, needles, thermometers, urethral 2015~
catheters and various components of medical monitoring apparatuses which may advantageously be coated with the composition of the invention.
Representative coating compositions of the invention are listed in Table II of Example II. The coatings of the invention were applied to a polymeric substrate by the procedure of Example III
and tested for stability as described in Example IV
and were found to be substantially more stable than coatings prepared from prior art PUs, Substrates coated with the composition of the invention are substantially dry until contacted with a liquid whereupon they are instantly rendered lubricious. Lubricity of the coated surfaces were determined by measuring their coefficients of friction using the Instron Model 1122 Universal Testing Machine by the procedure described in Example V. Lubricity data is given in Table II
which accompanies Example II.
The following examples are given to further illustrate the invention but are not to be considered as limitative thereof.
EXAMPLE I
Bulk Synthesis PEG was dried at 60 to 70~C under vacuum (4-6 mm Hg) for 4 to 6 hours to remove moisture. Water content (Carl Fisher titration) and polyol hydroxyl number ~phthalic anhydride-pyridine method) were determined to adjust formulation stoichiometry. MDI
was filtered to remove any reacted diisocyanate and vacuum stripped (4-6 mm Hg) for 2 to 4 hours. The stoichimetric amounts of PEG and BDO were placed in the polymerization vessel and degassed at 60~ for 30 minutes. Then, the stoichiometric amount of MDI
(1.02 index) was added and the mixture stirred vigorously until the polymerization temperature reached about 85 to 90~C. The polymer was discharged and postcured at 125~C for 30 minutes.
Solution Synthesis Solution polymerization at 25~ total solids was performed in DMAC under a nitrogen atmosphere. PEG
was dried at 60 to 70~C under vacuum (4-6 mm Hg) for 4 to 6 hours to remove moisture. Water content (Carl Fisher titration) and polyol hydroxyl number (phthalic anhydride-pyridine method) were determined to adjust formulation stoichiometry. MDI was filtered to remove any reacted diisocyanate and vacuum stripped (4-6 mm Hg) for 2 to 4 hours.
Stoichiometric amounts of PEG and BDO were placed in the polymerization vessel and degassed at 60~C for 30 minutes. Two thirds of the total solvent used (DMAC) was added to the PEG-extender mixture. The stoichiometric (1.02 Index) amount of MDI was dissolved in the remaining DMAC and the solution was added dropwise to the polymerization vessel. The polymerization medium was maintained at 60 to 70~C
and constantly stirred. A polymerization time of four hours at 60 to 70~C was sufficient for adequate formation.
Z~)~561~
TABLE I
Typical HPEUs of the Invention HPEU HS CONTENTPOLYETHER NUMBER OF EQUIVALENTS OF
NO. (% WT) TYPE MDI BDO PEG
1 30 PEG 14501.02 0.506 0.494 2 35 PEG 14501.02 0.597 0.403 3 40 PEG 14501.02 0.667 0.333 4 45 PEG 14501.02 0.738 0.262 PEG 14501.02 0.772 0.228 6 55 PEG 14501.02 0.821 0.179 7 60 PEG 14501.02 0.845 0.155 E~MPLE II
Preparation of Lubricious Coatinq The HPEU of Example I was dissolved in DMF and the desired amount of PVP (K-90, Aldrich) was added. The solution concentration and the solvent ratio of the lubricious coating solution were adjusted by adding THF.
znlS61~
TABLE II
Examples of HPEU Based Lubricious Coating Compositions of the Invention COMPOSITION ~PEU ~PEU/PVP CONC~UTP~TTON SOLV~NTS & COEFFICIENI*
NO. HS~ RATIO(~ SOLID) RATIOSOF FRICTION
1 40 3~7 6 DffF/T~F (3/2) 0.114 + 0.006 2 40 1/1 6 "0.118 + 0.013 3 40 3/7 10 "0.107 + 0.004 4 40 1/1 10 "0.130 + 0.004 0 5 50 3/7 6 "0.108 + 0.012 6 50 3/7 10 0.067 + 0.007 7 50 1/1 10 "0.121 + 0.003 8 60 3/7 6 "0.094 + 0.003 9 60 3/~ 10 "0.085 + 0.003 1 5 10 60 1/1 10 "0.114 + 0.004 PVC CONTXOL (UNCOATED FXOSTED PVC TUBrNG) 0.986 + 0.048 * Detern~d br the pLoeed~,~ of EYample V.
EXAMPLE III
Coating Application Procedure The lubricious coatings of this invention were applied to PVC tubing by dip coating. Tubing samples were cut to desired lengths and were heat sealed at one end to contain the coating application to the outer surface only. The thickness of the 2 5 applied coating was adjusted by changing the dipping rate and the coating solution concentration. The tubing samples were vertically dipped into the 2~156~
coating solutions of Table II (6-10~ solids). The coated samples were first placed in a convection oven at 125~C for 30 seconds, then transferred to another convection oven at 65~C for 30 to 45 minutes to remove the solvents.
EXAMPLE IV
Lubricious Coating Stability Test The following tests were employed for determining the stability of the lubricious coatings;
1. The coated tubing samples were placed in distilled water for a few minutes (2 to 5 minutes) and examined visually for signs of delamination. No lubricity testing was performed on samples that delaminated; they were considered unstable.
2. The lubricious coatings that passed the first test were evaluated in the lubricity test.
Samples that delaminated during the lubricity test were also considered unstable.
3. Samples that withstood tests 1 and 2, were then tested for the coating adhesion strength as follows: samples were placed in distilled water and vigorously stirred at room temperature for one hour. Samples were visually inspected for lubricious coating delamination.
4. Finally, samples were stored in distilled water at room temperature for 1 to 5 days, then 2nls6i ~
- tested for forced delamination by subjecting to the lubricity test. Samples were examined for signs of delamination during the lubricity test.
The lubricious coating stability of the samples that successfully passed test 1 to 4 was rated as excellent. The lubricious coating stability of the samples that failed at any of these four tests were considered unstable.
EXAMPLE V
loLubricity Testinq The lubricity of the disclosed formulations were evaluated by comparing the surface coefficients of friction of the coated samples with that of the uncoated substrate. Surface coefficients of friction were determined using an Instron Universal Testing Machine, Model 1122, and the drag generated between the sample and a natural rubber substrate was measured. Test samples were secured in a water filled trough and were soaked for 5 minutes before testing. A piece of clean natural pure gum rubber (lab grade, Fisher Scientific) was placed in contact with the test sample under water and pulled at a constant speed (5 cm/min) under a standard applied load (532 gm). The measured drag force in newtons (N) was converted--to the coefficient of friction (CF) using the following equation:
Drag Force (N) - Internal Friction (N) CF =
0.0098 (N/gm) x Applied Load (gm) ~n~
where the internal friction is the drag generated by the friction apparatus in the absence of sample contact.
EXAMPLE VI
Preparation of Prior Art Coatings and Comparative Study with Coatinqs of the Invention A. NEPEU Synthesis:
Polytetramethyleneoxide glycol of 1000 molecular weight, (Terathane 1000, DuPont), was dried at 60 to 70~C under vacuum (4 to 6 mm Hg) for 4 to 6 hours to remove moisture. MDI was filtered to remove any reacted diisocyanate and vacuum stripped (4 to 6 mm Hg) for 2 to 4 hours. Polyol was weighed and placed in the polymerization vessel. Then the weighed amount of MDI (30%, 40%, 50% by weight) was added, and the mixture stirred vigorously for 15 minutes. The NEPEU thus obtained was stored under nitrogen in a tightly closed jar.
B. NEHPEU Synthesis: ~
PEG of 1450 molecular weight (Union Carbide) was dried at 60 to 70~C under vacuum (4 to 6 mm Hg) for 4 to 6 hours to remove moisture. MDI was filtered to remove any reacted diisocyanate and vacuum stripped (4 to 6 mm Hg) for 2 to 4 hours.
The PEG was weighed and placed in the polymerization vessel, the weighed amount of MDI (40%, 50% by weight) was added, and the mixture stirred ~201'5~
-vigorously for 15 minutes. The NEHPEU thus obtained was stored under nitrogen in a tightly closed jar.
C. NEPEU and NEHPEU based lubricious coatinq preparation:
The NEPEU and NEHPEU PUs from A and B were dissolved in DMF or DMAC. To this solution a desired amount of PVP (K-90, Aldrich) was added, and the polymer contents were dissolved by constant shaking. The solution concentration and the solvent ratio of the lubricious coating solution were adjusted by adding THF or MEK. The coatings were applied to PVC tubing as described in Example III
for stability and lubricity tests.
D. ESTANE 5703 based lubricious coatinq preparation and application:
To a mixture of 75 gm of DAA and 25 gm of MEK
were added 4 gm of PVP (K-90, Aldrich) and 2 gm of linear PU (Estane*5703, B.F. Goodrich). The polymer contents were dissolved by constant shaking. The resulting coating solution was applied to PVC tubing using the standard coating application procedure.
E. NEOREZ R940 based lubricious coatinq preparation and application:
To 47 gm of water and 10 gm of NMP were added 10 gm of PVP (K-90, Aldrich) and 33 gm of linear PU
aqueous dispersion (Neorez R940, ICI, formerly Polyvinyl Chemical Industries). The polymer contents were dissolved by constant shaking. The ~ ~a 1~5 ~ ~ ~
resulting solution was applied to PVC tubing using the standard coating application procedure.
The coatings the prior art described in A-E and applied to PVC tubing are listed in Table III as compositions 7-13 and may -be compared with compositions 1-6 of the invention. --TA~LEIII
COMPARATIVE LUBRIC-OUS COAnNG COMPOSmONS
COMPOSITION PU/PVP SOL. CONC SOLVENr'S ADHESION COEFFlClENT
NO. PU RATIO (% SOLID) AND RAnOS STABILIl-Y OF FRICllON
- I HPEU 40% HS 3/7 6 DMF/THF (3/Z E~cellent 0.114 + 0.006 2 HPEU409o HS 1/1 6 DMF/THF(3/t E~cellent 0.118 + 0.013 3 HPEU 409rC HS 3/7 10 DMF~THF (3/21 E~cellent Q107 + 0.004 4 HPEU S096 HS 3/7 6 DMFrlHF (3n,~ E~cellent 0.108 + Q012 S HPEU S0~o HS 1/1 10 DMF/THF (3/2) E~cellent 0.121 + Q003 6 HPEU 50% HS 3/7 10 DMF/THF(3/Z) E~cellent Q067 + 0.007 7 ESTANE S703 In S.7 DAA/MEK (3/1) Unstable N/A--8 NEOREZ R940 1/1 22 ~ Unstable N/A
9 NEPEU-30 1/1 6 DMAC/MEK (3/2) Unstable. N/A
NEPEU40 1/1 6 DMAC/MEK (3n) Ulutable N/A
NEPEU-S0 1/1 6 DMACMEK (3/2) U~able N/A
12 NEHPEU-40 1/1 6 DMF/'IHF (3n) Unstable N/A
13 NEHPEU-50 1/1 6 DMF/THF (3n) Unstable N/A
~wATER~NMp~MEJcfDE~ + 'IE~ t~l 3 6/~ 6~n ~-Not ~ bk ~ 8 ~ ' - ' durulB tes~ing in ~ pk V
Claims (17)
1. A lubricious and biocompatible coating composition for a substrate comprising a substantially uniform blend of a hydrophilic polymer and an elastomeric segmented hydrophilic polyetherurethane which is the reaction product of a diisocyanate, a hydrophilic polyether glycol and a chain extender.
2. The composition of Claim 1 wherein said polymer is selected from the group consisting of polyhydroxyethyl methacrylate, polyacrylic acid, polyvinylmethyl ether, polyvinylpyridine, polyethyleneoxide and polyvinylpyrrolidone.
3. The composition of Claim 1 wherein said diisocyanate is selected from the group consisting of 4,4'-diphenylmethane diisocyanate, 4,4'-dicyclo-hexylmethane diisocyanate, isophorone diisocyanate and hexamethylene diisocyanate.
4. The composition of Claim 1 wherein said hydrophilic polyetherglycol is polyethyleneoxide glycol.
5, The composition of Claim 1 wherein said chain extender is selected from the group consisting of a diol, a diamine and amino alcohol.
6. The composition of Claim 5 wherein said diol is selected from the group consisting of ethylene glycol, diethylene glycol, triethylene glycol, 1,2-propanediol, 1,3-propanediol, 1,4-butanediol, 1,6-hexanediol, 1,4-bis-hydro-xymethyl cyclohexane and hydroquinone dihydroxyethyl ether.
7. The composition of Claim 1 further including a reagent selected from the group consisting of an antimicrobial agent, flow aid, flatting agent, plasticizer, heat stabilizer, and surface cure modifier.
8. The composition of Claim 1 wherein said elastomeric segmented polyetherurethane has a hard segment content of about 25 to 60% by weight.
9 The composition of Claim 1 wherein the ratio of said hydrophilic polyetherurethane to said hydrophilic polymer is about 25 to 0.05.
10. A lubricious and hemocompatible coating composition comprising a substantially uniform blend of polyvinylpyrrolidone and an elastomeric segmented hydrophilic polyetherurethane which is the reaction product of 4,4'-diphenylmethane diisocyanate, polyethylene oxide glycol and 1,4-butanediol having a hard segment content of about 25 to 60% by weight.
11. A method for lubricating a polymeric surface comprising coating onto a polymeric surface a composition comprising a substantially uniform blend of a hydrophilic polymer and an elastomeric segmented hydrophilic polyetherurethane which is the reaction product of a diisocyanate, a hydrophilic polyether glycol and a chain extender to give a coated surface and contacting said coated surface - 24 - :
with a liquid.
with a liquid.
12. The method of Claim 11 wherein said polymer is selected from the group consisting of polyhydroxyethyl methacrylate, polyacrylic acid, polyvinylmethyl ether, polyvinylpyridine, polyethyleneox}de and polyvinylpyrrolidone.
13. The method of Claim 11 wherein said diisocyanate is selected from the group consisting of 4,4'-diphenylmethane diisocyanate, 4,4'-dicyclo-hexylmethane dilsocyanate, isophorone diisocyanate and hexamethylene diisocyanate.
14. The method of Claim 11 wherein said hydrophilic polyether glycol is polyethyleneoxide glycol.
15. The method of Claim 11 wherein said coating step is performed by dipping.
16. The method of Claim 11 wherein said composition further includes a reagent selected from the group consisting of an antimicrobial agent, flow aid, flatting agent, plasticizer, heat stabilizer, and surface cure modifier.
17. A method for lubricating a polymeric surface comprising:
a) preparing a composition comprising a substantially uniform blend of polyvinylpyrrolidone and an elastomeric segmented hydrophilic polyetherurethane which is the reaction product of 4,4'-diphenylmethane diisocyanate, polyethylene oxide glycol and 1,4-butanediol having a hard segment content of about 25 to 60%;
b) coating said composition onto a polymeric substrate; and c) contacting the coated surface with an aqueous liquid.
a) preparing a composition comprising a substantially uniform blend of polyvinylpyrrolidone and an elastomeric segmented hydrophilic polyetherurethane which is the reaction product of 4,4'-diphenylmethane diisocyanate, polyethylene oxide glycol and 1,4-butanediol having a hard segment content of about 25 to 60%;
b) coating said composition onto a polymeric substrate; and c) contacting the coated surface with an aqueous liquid.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US347,133 | 1989-05-04 | ||
| US07/347,133 US4990357A (en) | 1989-05-04 | 1989-05-04 | Elastomeric segmented hydrophilic polyetherurethane based lubricious coatings |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2015619A1 CA2015619A1 (en) | 1990-11-05 |
| CA2015619C true CA2015619C (en) | 1997-09-16 |
Family
ID=23362472
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002015619A Expired - Fee Related CA2015619C (en) | 1989-05-04 | 1990-04-27 | Elastomeric segmented hydrophilic polyetherurethane based lubricious coatings |
Country Status (8)
| Country | Link |
|---|---|
| US (1) | US4990357A (en) |
| EP (1) | EP0396431B1 (en) |
| JP (1) | JPH0321677A (en) |
| AT (1) | ATE109497T1 (en) |
| CA (1) | CA2015619C (en) |
| DE (1) | DE69011182T2 (en) |
| ES (1) | ES2060948T3 (en) |
| IE (1) | IE901462L (en) |
Families Citing this family (116)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE69108895T2 (en) * | 1990-01-05 | 1995-08-24 | Goodrich Co B F | CHAIN EXTENDED LOW MOLECULAR WEIGHT DETECTING POLYOXIRANES FOR ELECTROSTATIC APPLICATIONS. |
| US5574104A (en) * | 1990-01-05 | 1996-11-12 | The B. F. Goodrich Company | Chain extended low molecular weight polyoxiranes and electrostatic dissipating blend compositions based thereon |
| US5179174A (en) * | 1990-04-23 | 1993-01-12 | C. R. Bard, Inc. | Flexible lubricious organic coatings |
| US5160790A (en) * | 1990-11-01 | 1992-11-03 | C. R. Bard, Inc. | Lubricious hydrogel coatings |
| US5295978A (en) * | 1990-12-28 | 1994-03-22 | Union Carbide Chemicals & Plastics Technology Corporation | Biocompatible hydrophilic complexes and process for preparation and use |
| US5061424A (en) * | 1991-01-22 | 1991-10-29 | Becton, Dickinson And Company | Method for applying a lubricious coating to an article |
| GB9112267D0 (en) * | 1991-06-07 | 1991-07-24 | Biocompatibles Ltd | Polymeric coating |
| US5443907A (en) * | 1991-06-18 | 1995-08-22 | Scimed Life Systems, Inc. | Coating for medical insertion guides |
| CA2068584C (en) * | 1991-06-18 | 1997-04-22 | Paul H. Burmeister | Intravascular guide wire and method for manufacture thereof |
| US5242428A (en) * | 1991-10-04 | 1993-09-07 | Aubrey Palestrant | Apparatus for wetting hydrophilic-coated guide wires and catheters |
| US5250620A (en) * | 1991-11-21 | 1993-10-05 | Miles Inc. | Hydrophilic polyvinylpyrrolidone compositions having a low coefficient of friction |
| EP0574160B1 (en) * | 1992-06-10 | 1997-02-19 | Maxxim Medical, Inc. | Flexible rubber article and method of making |
| DK172393B1 (en) * | 1992-06-10 | 1998-05-18 | Maersk Medical As | Process for producing an article having friction-reducing surface coating, coating material for use in the manufacture of such article, and using an osmolality-increasing compound in slurry or emulsified form in the coating material |
| US5881386A (en) † | 1993-12-23 | 1999-03-16 | Maxxim Medical, Inc. | Flexible polyvinyl chloride article and method of making |
| US5545150A (en) * | 1994-05-06 | 1996-08-13 | Endoscopic Concepts, Inc. | Trocar |
| US5662960A (en) * | 1995-02-01 | 1997-09-02 | Schneider (Usa) Inc. | Process for producing slippery, tenaciously adhering hydrogel coatings containing a polyurethane-urea polymer hydrogel commingled with a poly (n-vinylpyrrolidone) polymer hydrogel |
| DE69625799T2 (en) * | 1995-02-01 | 2003-10-23 | Schneider Usa Inc | METHOD FOR HYDROPHILIZING HYDROPHOBIC POLYMERS |
| US5919570A (en) * | 1995-02-01 | 1999-07-06 | Schneider Inc. | Slippery, tenaciously adhering hydrogel coatings containing a polyurethane-urea polymer hydrogel commingled with a poly(N-vinylpyrrolidone) polymer hydrogel, coated polymer and metal substrate materials, and coated medical devices |
| US6017577A (en) * | 1995-02-01 | 2000-01-25 | Schneider (Usa) Inc. | Slippery, tenaciously adhering hydrophilic polyurethane hydrogel coatings, coated polymer substrate materials, and coated medical devices |
| US5576072A (en) * | 1995-02-01 | 1996-11-19 | Schneider (Usa), Inc. | Process for producing slippery, tenaciously adhering hydrogel coatings containing a polyurethane-urea polymer hydrogel commingled with at least one other, dissimilar polymer hydrogel |
| DE69637954D1 (en) * | 1995-02-01 | 2009-07-30 | Boston Scient Scimed Inc | Medical device containing a chemically treated metal substrate |
| US5731087A (en) * | 1995-06-07 | 1998-03-24 | Union Carbide Chemicals & Plastics Technology Corporation | Lubricious coatings containing polymers with vinyl and carboxylic acid moieties |
| US5620738A (en) * | 1995-06-07 | 1997-04-15 | Union Carbide Chemicals & Plastics Technology Corporation | Non-reactive lubicious coating process |
| US6284839B1 (en) | 1995-12-29 | 2001-09-04 | The B.F. Goodrich Company | Blends of thermoplastic polymers, electrostatic dissipative polymers and electrostatic dissipative enhancers |
| US5800412A (en) * | 1996-10-10 | 1998-09-01 | Sts Biopolymers, Inc. | Hydrophilic coatings with hydrating agents |
| EP0946222A1 (en) * | 1996-12-13 | 1999-10-06 | Data Sciences International, Inc. | Biocompatible medical devices with polyurethane surface |
| US5997517A (en) | 1997-01-27 | 1999-12-07 | Sts Biopolymers, Inc. | Bonding layers for medical device surface coatings |
| US6221467B1 (en) | 1997-06-03 | 2001-04-24 | Scimed Life Systems, Inc. | Coating gradient for lubricious coatings on balloon catheters |
| USD426635S (en) * | 1998-08-18 | 2000-06-13 | Genicon, Lc | Combination trocar, cannula, and valve |
| DE19837377A1 (en) * | 1998-08-18 | 2000-02-24 | Basf Ag | Latent cross-linkable aqueous polyurethane dispersion, useful as an impregnating agent, coating and adhesive comprises a polyurethane having hydrophilic and carbodiimide groups. |
| US6596401B1 (en) | 1998-11-10 | 2003-07-22 | C. R. Bard Inc. | Silane copolymer compositions containing active agents |
| US6329488B1 (en) | 1998-11-10 | 2001-12-11 | C. R. Bard, Inc. | Silane copolymer coatings |
| US6340465B1 (en) * | 1999-04-12 | 2002-01-22 | Edwards Lifesciences Corp. | Lubricious coatings for medical devices |
| US6610035B2 (en) | 1999-05-21 | 2003-08-26 | Scimed Life Systems, Inc. | Hydrophilic lubricity coating for medical devices comprising a hybrid top coat |
| CA2392960C (en) * | 1999-11-29 | 2009-11-03 | Henkel Kommanditgesellschaft Auf Aktien | Adhesion promoters for monomer-free reactive polyurethanes |
| USD449887S1 (en) | 2000-01-26 | 2001-10-30 | Genicon Lc | Combined obturator, cannula and valve assembly |
| US7153319B1 (en) | 2000-01-26 | 2006-12-26 | Genico, Inc. | Trocar system having shielded trocar |
| USD443360S1 (en) | 2000-03-22 | 2001-06-05 | Dexterity Surgical Inc. | Distal end of obturator for a trocar |
| US20020120333A1 (en) * | 2001-01-31 | 2002-08-29 | Keogh James R. | Method for coating medical device surfaces |
| US6756449B2 (en) * | 2002-02-27 | 2004-06-29 | Medtronic, Inc. | AnB block copolymers containing poly (vinyl pyrrolidone) units, medical devices, and methods |
| US7008979B2 (en) * | 2002-04-30 | 2006-03-07 | Hydromer, Inc. | Coating composition for multiple hydrophilic applications |
| US6770729B2 (en) * | 2002-09-30 | 2004-08-03 | Medtronic Minimed, Inc. | Polymer compositions containing bioactive agents and methods for their use |
| US20040220534A1 (en) * | 2003-04-29 | 2004-11-04 | Martens Paul W. | Medical device with antimicrobial layer |
| US7544381B2 (en) * | 2003-09-09 | 2009-06-09 | Boston Scientific Scimed, Inc. | Lubricious coatings for medical device |
| ATE417895T1 (en) * | 2003-10-07 | 2009-01-15 | Coloplast As | COMPOSITION WHICH CAN BE USED AS AN ADHESIVE AND USE OF SUCH A COMPOSITION |
| US20070009582A1 (en) * | 2003-10-07 | 2007-01-11 | Madsen Niels J | Composition useful as an adhesive and use of such a composition |
| US20050129733A1 (en) * | 2003-12-09 | 2005-06-16 | Milbocker Michael T. | Surgical adhesive and uses therefore |
| DE102004049609A1 (en) * | 2004-10-12 | 2006-04-13 | Mitsubishi Polyester Film Gmbh | Polyester film with hydrophilic coating, process for its preparation and its use |
| US20060204535A1 (en) * | 2005-02-25 | 2006-09-14 | Johnson Johnnie M | Cell-friendly cannula and needle |
| US20060233852A1 (en) * | 2005-04-19 | 2006-10-19 | Promethean Surgical Devices | Prosthetic for tissue reinforcement |
| US20060240253A1 (en) * | 2005-04-22 | 2006-10-26 | Cardiac Pacemakers, Inc. | Guidewire and tube with lubricious coating |
| US20060240060A1 (en) * | 2005-04-22 | 2006-10-26 | Cardiac Pacemakers, Inc. | Lubricious compound and medical device made of the same |
| US20060240059A1 (en) * | 2005-04-22 | 2006-10-26 | Cardiac Pacemakers, Inc. | Lubricious eluting polymer blend and coating made from the same |
| US20060241000A1 (en) * | 2005-04-22 | 2006-10-26 | Cardiac Pacemakers, Inc. | Lubricious compound and medical device made of the same |
| DK1885871T3 (en) | 2005-05-17 | 2012-07-02 | Radiometer Medical Aps | Enzyme sensor with a cover membrane layer of a porous polymer material covered by a hydrophilic polymer |
| EP1885871B1 (en) * | 2005-05-17 | 2012-05-30 | Radiometer Medical ApS | Enzyme sensor with a cover membrane layer covered by a hydrophilic polymer |
| US20070129690A1 (en) | 2005-12-02 | 2007-06-07 | Joel Rosenblatt | Catheter with polymeric coating |
| EP1979016B1 (en) | 2006-02-01 | 2015-07-01 | Hollister Incorporated | Methods of applying a hydrophilic coating to a substrate, and substrates having a hydrophilic coating |
| US9289279B2 (en) | 2006-10-06 | 2016-03-22 | Promethean Surgical Devices, Llc | Apparatus and method for limiting surgical adhesions |
| US20080260944A1 (en) * | 2007-04-20 | 2008-10-23 | Sun Chemical Corporation | Water-Activated Non Blocking Adhesive |
| US20100056646A1 (en) * | 2008-03-12 | 2010-03-04 | Shalaby Shalaby W | Hydroswellable, segmented, aliphatic polyurethane ureas and intra-articular devices therefrom |
| US20090233887A1 (en) * | 2008-03-12 | 2009-09-17 | Shalaby Shalaby W | Hydroswellable, Segmented, Aliphatic Polyurethanes and Polyurethane Ureas |
| US20110076712A1 (en) * | 2008-06-13 | 2011-03-31 | Xy, Llc. | Lubricious microfludic flow path system |
| US8049061B2 (en) | 2008-09-25 | 2011-11-01 | Abbott Cardiovascular Systems, Inc. | Expandable member formed of a fibrous matrix having hydrogel polymer for intraluminal drug delivery |
| US8500687B2 (en) | 2008-09-25 | 2013-08-06 | Abbott Cardiovascular Systems Inc. | Stent delivery system having a fibrous matrix covering with improved stent retention |
| US8226603B2 (en) * | 2008-09-25 | 2012-07-24 | Abbott Cardiovascular Systems Inc. | Expandable member having a covering formed of a fibrous matrix for intraluminal drug delivery |
| US8076529B2 (en) * | 2008-09-26 | 2011-12-13 | Abbott Cardiovascular Systems, Inc. | Expandable member formed of a fibrous matrix for intraluminal drug delivery |
| US20100082097A1 (en) * | 2008-10-01 | 2010-04-01 | Joel Rosenblatt | Article Containing Segregated Biguanide and Lewis Acid |
| EP2392378B1 (en) * | 2009-01-30 | 2017-03-15 | Hisamitsu Pharmaceutical Co., Inc. | Microneedle device |
| US8691235B2 (en) * | 2009-04-03 | 2014-04-08 | Poly-Med, Inc. | Absorbable crystalline polyether-ester-urethane-based bioactive luminal liner compositions |
| US20100285085A1 (en) * | 2009-05-07 | 2010-11-11 | Abbott Cardiovascular Systems Inc. | Balloon coating with drug transfer control via coating thickness |
| WO2011005840A2 (en) | 2009-07-07 | 2011-01-13 | Med Institute, Inc. | Hydrogel enhanced medical devices |
| US8821455B2 (en) * | 2009-07-09 | 2014-09-02 | Becton, Dickinson And Company | Antimicrobial coating for dermally invasive devices |
| US20110144689A1 (en) * | 2009-12-15 | 2011-06-16 | Med Institute, Inc. | Occlusion Device |
| US20110200828A1 (en) * | 2010-02-16 | 2011-08-18 | Biocoat Incorporated | Hydrophilic coatings for medical devices |
| KR102139022B1 (en) | 2010-07-30 | 2020-07-29 | 알콘 인코포레이티드 | A silicone hydrogel lens with a crosslinked hydrophilic coating |
| HUE029018T2 (en) | 2011-10-12 | 2017-02-28 | Novartis Ag | Method for making uv-absorbing ophthalmic lenses by coating |
| BR112014017675B1 (en) | 2012-01-18 | 2021-06-22 | Surmodics, Inc | COATING FOR A LUBRICATING MEDICAL DEVICE WITH LOW PARTICULATE CONTENT, MEDICAL DEVICE AND METHOD OF PRODUCTION |
| WO2014095690A1 (en) | 2012-12-17 | 2014-06-26 | Novartis Ag | Method for making improved uv-absorbing ophthalmic lenses |
| DE102012223422A1 (en) * | 2012-12-17 | 2014-06-18 | Henkel Ag & Co. Kgaa | Low-modulus silane-terminated PU prepolymers |
| US9750928B2 (en) | 2013-02-13 | 2017-09-05 | Becton, Dickinson And Company | Blood control IV catheter with stationary septum activator |
| US9695323B2 (en) | 2013-02-13 | 2017-07-04 | Becton, Dickinson And Company | UV curable solventless antimicrobial compositions |
| US9327095B2 (en) | 2013-03-11 | 2016-05-03 | Becton, Dickinson And Company | Blood control catheter with antimicrobial needle lube |
| US9750927B2 (en) | 2013-03-11 | 2017-09-05 | Becton, Dickinson And Company | Blood control catheter with antimicrobial needle lube |
| US9714361B2 (en) | 2013-03-15 | 2017-07-25 | Lake Region Manfacturing, Inc. | Oxirane (ethylene oxide) polyurethane coatings |
| US9255173B2 (en) | 2013-03-15 | 2016-02-09 | Lake Region Manufacturing, Inc. | Oxirane (ethylene oxide) polyurethane coatings |
| US9708087B2 (en) | 2013-12-17 | 2017-07-18 | Novartis Ag | Silicone hydrogel lens with a crosslinked hydrophilic coating |
| US10376686B2 (en) | 2014-04-23 | 2019-08-13 | Becton, Dickinson And Company | Antimicrobial caps for medical connectors |
| US9789279B2 (en) | 2014-04-23 | 2017-10-17 | Becton, Dickinson And Company | Antimicrobial obturator for use with vascular access devices |
| US9675793B2 (en) | 2014-04-23 | 2017-06-13 | Becton, Dickinson And Company | Catheter tubing with extraluminal antimicrobial coating |
| US10232088B2 (en) | 2014-07-08 | 2019-03-19 | Becton, Dickinson And Company | Antimicrobial coating forming kink resistant feature on a vascular access device |
| CN106715101B (en) | 2014-08-26 | 2019-11-05 | 诺华股份有限公司 | Method for applying stable coating in silicone hydrogel contact lens on piece |
| US10070686B2 (en) | 2014-08-27 | 2018-09-11 | Nike, Inc. | Soil-shedding article of footwear, components thereof, and methods of making the article |
| EP3169175B1 (en) | 2014-08-27 | 2020-06-17 | NIKE Innovate C.V. | Articles of footwear, apparel, and sports equipment with water absorbtion properties |
| US10314364B2 (en) | 2014-08-27 | 2019-06-11 | Nike, Inc. | Soil-shedding article of footwear, and method of using the same |
| GB2532837B (en) | 2014-08-27 | 2017-10-25 | Nike Innovate Cv | Article of footwear with soil-shedding performance |
| US10064447B2 (en) | 2014-08-27 | 2018-09-04 | Nike, Inc. | Article of footwear with soil-shedding performance |
| US10124088B2 (en) | 2014-09-29 | 2018-11-13 | Surmodics, Inc. | Lubricious medical device elements |
| SG11201802940YA (en) | 2015-10-09 | 2018-05-30 | Kpr U S Llc | Compression garment compliance |
| BR112018007787B1 (en) | 2015-10-18 | 2021-08-10 | Allegiance Corporation | ELASTOMERIC ARTICLE HAVING A COATING ON IT, METHOD OF COATING AN ELASTOMERIC ARTICLE AND COATING COMPOSITION |
| US10493244B2 (en) | 2015-10-28 | 2019-12-03 | Becton, Dickinson And Company | Extension tubing strain relief |
| EP3391101B1 (en) | 2015-12-15 | 2020-07-08 | Alcon Inc. | Method for applying stable coating on silicone hydrogel contact lenses |
| US11174447B2 (en) | 2015-12-29 | 2021-11-16 | Surmodics, Inc. | Lubricious coatings with surface salt groups |
| US10342898B2 (en) | 2015-12-29 | 2019-07-09 | Surmodics, Inc. | Lubricious coatings with surface salt groups |
| US10455893B2 (en) | 2016-03-02 | 2019-10-29 | Nike, Inc. | Hydrogel with mesh for soil deflection |
| US10531705B2 (en) | 2016-03-02 | 2020-01-14 | Nike, Inc. | Hydrogel tie layer |
| US10362834B2 (en) | 2016-03-02 | 2019-07-30 | Nike, Inc. | Hydrogel connection |
| US10675609B2 (en) | 2016-03-02 | 2020-06-09 | Nike, Inc. | Articles with soil-shedding performance |
| EP3984568A1 (en) | 2016-07-14 | 2022-04-20 | Hollister Incorporated | Hygienic medical devices having hydrophilic coatings and methods of forming the same |
| CN109923151B (en) | 2016-11-03 | 2021-08-20 | 3M创新有限公司 | Silicone copolymers, methods of manufacture, and articles |
| AU2018261179B2 (en) | 2017-05-04 | 2023-02-09 | Hollister Incorporated | Lubricious hydrophilic coatings and methods of forming the same |
| TWI700175B (en) | 2017-08-01 | 2020-08-01 | 荷蘭商耐基創新公司 | Method of manufacturing a component of an outsole for use in an article of footwear |
| CN115251519A (en) | 2017-10-19 | 2022-11-01 | 耐克创新有限合伙公司 | Outsole and method of manufacturing an outsole |
| CN111386478B (en) | 2017-12-13 | 2023-11-14 | 爱尔康公司 | Zhou Pao and month polishing gradient contact lens |
| US10899944B2 (en) | 2018-10-29 | 2021-01-26 | Lake Region Manufacturing, Inc. | Polyurethane urea-containing adipic acid dihydrazide where active hydrogens react with the epoxy group found on glycidol to form a diol |
| US11359156B2 (en) | 2019-10-21 | 2022-06-14 | Biocoat, Inc. | UV cure basecoatings for medical devices |
Family Cites Families (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5424988B2 (en) * | 1972-02-24 | 1979-08-24 | ||
| IN141398B (en) * | 1973-05-16 | 1977-02-26 | Ethicon Inc | |
| JPS51139900A (en) * | 1975-05-15 | 1976-12-02 | Grace W R & Co | Hydrophilic polyurethane foam like natural sponge |
| US4100309A (en) * | 1977-08-08 | 1978-07-11 | Biosearch Medical Products, Inc. | Coated substrate having a low coefficient of friction hydrophilic coating and a method of making the same |
| US4377010A (en) * | 1978-11-08 | 1983-03-22 | The Secretary Of State For Defence In Her Britannic Majesty's Government Of The United Kingdom Of Great Britain And Northern Ireland | Biocompatible material comprising a base polymer bulk graft polymerized with an ethylenically unsaturated carboxylic acid |
| US4373009A (en) * | 1981-05-18 | 1983-02-08 | International Silicone Corporation | Method of forming a hydrophilic coating on a substrate |
| US4497914A (en) * | 1982-07-16 | 1985-02-05 | C. R. Bard, Inc. | Breathable ostomy gasket composition |
| US4642267A (en) * | 1985-05-06 | 1987-02-10 | Hydromer, Inc. | Hydrophilic polymer blend |
| US4767414A (en) * | 1985-05-16 | 1988-08-30 | Becton, Dickinson And Company | Ionizing plasma lubricant method |
| US4795475A (en) * | 1985-08-09 | 1989-01-03 | Walker Michael M | Prosthesis utilizing salt-forming oxyacids for bone fixation |
| US4720521A (en) * | 1985-12-03 | 1988-01-19 | Becton, Dickinson And Company | Film-forming silicone compositions having lubricating properties |
| DE3700571A1 (en) * | 1987-01-10 | 1988-07-21 | Bayer Ag | MIXTURES OF AQUEOUS POLYMER DISPERSIONS AND THEIR USE AS COATING MEASURES |
| US4906240A (en) * | 1988-02-01 | 1990-03-06 | Matrix Medica, Inc. | Adhesive-faced porous absorbent sheet and method of making same |
-
1989
- 1989-05-04 US US07/347,133 patent/US4990357A/en not_active Expired - Fee Related
-
1990
- 1990-04-24 IE IE901462A patent/IE901462L/en unknown
- 1990-04-27 CA CA002015619A patent/CA2015619C/en not_active Expired - Fee Related
- 1990-05-04 DE DE69011182T patent/DE69011182T2/en not_active Expired - Fee Related
- 1990-05-04 EP EP90304911A patent/EP0396431B1/en not_active Expired - Lifetime
- 1990-05-04 ES ES90304911T patent/ES2060948T3/en not_active Expired - Lifetime
- 1990-05-04 AT AT90304911T patent/ATE109497T1/en not_active IP Right Cessation
- 1990-05-07 JP JP2117280A patent/JPH0321677A/en active Pending
Also Published As
| Publication number | Publication date |
|---|---|
| DE69011182T2 (en) | 1994-12-01 |
| EP0396431B1 (en) | 1994-08-03 |
| JPH0321677A (en) | 1991-01-30 |
| CA2015619A1 (en) | 1990-11-05 |
| DE69011182D1 (en) | 1994-09-08 |
| ATE109497T1 (en) | 1994-08-15 |
| US4990357A (en) | 1991-02-05 |
| ES2060948T3 (en) | 1994-12-01 |
| IE901462L (en) | 1990-11-04 |
| EP0396431A1 (en) | 1990-11-07 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2015619C (en) | Elastomeric segmented hydrophilic polyetherurethane based lubricious coatings | |
| EP0496305B1 (en) | Method for applying a lubricious coating to an article | |
| US5558900A (en) | One-step thromboresistant, lubricious coating | |
| EP0439908B1 (en) | Lubricous coatings, medical articles containing same and method for their preparation | |
| US5160790A (en) | Lubricious hydrogel coatings | |
| EP0379156B1 (en) | Improved hydrophilic lubricious coatings | |
| AU711425B2 (en) | Fluoroligomer surface modifiers for polymers and articles made therefrom | |
| US5295978A (en) | Biocompatible hydrophilic complexes and process for preparation and use | |
| JP5477071B2 (en) | Medical device with lubricity when wet | |
| EP0907384B2 (en) | Medical device | |
| US5059269A (en) | Method of making an article having a hemocompatible surface | |
| IE911354A1 (en) | Flexible lubricious organic coatings | |
| CA2039393C (en) | Melt processable polyurethaneurea copolymers and method for their preparation | |
| US4939007A (en) | Article having a hemocompatible surface | |
| US6160032A (en) | Biocompatible coating composition | |
| KR101235225B1 (en) | Wet lubricant surface coating having excellent durability, method for surface coating, and a medical device having the surface coating | |
| JP5375606B2 (en) | Composition for wet lubrication surface coating excellent in durability, coating liquid, surface coating, surface coating method, and medical device having the surface coating | |
| JPS6371259A (en) | Stay catheter |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKLA | Lapsed |