NO20023343L - Coating of implantable ophthalmic lenses to reduce edge glare - Google Patents
Coating of implantable ophthalmic lenses to reduce edge glare Download PDFInfo
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- NO20023343L NO20023343L NO20023343A NO20023343A NO20023343L NO 20023343 L NO20023343 L NO 20023343L NO 20023343 A NO20023343 A NO 20023343A NO 20023343 A NO20023343 A NO 20023343A NO 20023343 L NO20023343 L NO 20023343L
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- coating material
- hydrophilic polymer
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- hydrophobic
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- 238000000576 coating method Methods 0.000 title claims description 84
- 239000011248 coating agent Substances 0.000 title claims description 79
- 230000004313 glare Effects 0.000 title claims description 9
- 239000000463 material Substances 0.000 claims description 58
- 230000002209 hydrophobic effect Effects 0.000 claims description 35
- 229920001477 hydrophilic polymer Polymers 0.000 claims description 33
- 229920000058 polyacrylate Polymers 0.000 claims description 25
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 20
- 239000007943 implant Substances 0.000 claims description 17
- 238000000034 method Methods 0.000 claims description 13
- 229920000036 polyvinylpyrrolidone Polymers 0.000 claims description 12
- 235000013855 polyvinylpyrrolidone Nutrition 0.000 claims description 11
- 239000001267 polyvinylpyrrolidone Substances 0.000 claims description 11
- 239000000178 monomer Substances 0.000 claims description 8
- ILZXXGLGJZQLTR-UHFFFAOYSA-N 2-phenylethyl 2-methylprop-2-enoate Chemical compound CC(=C)C(=O)OCCC1=CC=CC=C1 ILZXXGLGJZQLTR-UHFFFAOYSA-N 0.000 claims description 7
- HPSGLFKWHYAKSF-UHFFFAOYSA-N 2-phenylethyl prop-2-enoate Chemical compound C=CC(=O)OCCC1=CC=CC=C1 HPSGLFKWHYAKSF-UHFFFAOYSA-N 0.000 claims description 6
- 239000003795 chemical substances by application Substances 0.000 claims description 5
- 239000004615 ingredient Substances 0.000 claims description 5
- 230000003287 optical effect Effects 0.000 claims description 5
- 229920002338 polyhydroxyethylmethacrylate Polymers 0.000 claims description 5
- 125000003118 aryl group Chemical group 0.000 claims description 4
- 229920002189 poly(glycerol 1-O-monomethacrylate) polymer Polymers 0.000 claims description 4
- 229920002401 polyacrylamide Polymers 0.000 claims description 4
- 230000000903 blocking effect Effects 0.000 claims description 3
- 239000000975 dye Substances 0.000 claims description 3
- 125000000956 methoxy group Chemical group [H]C([H])([H])O* 0.000 claims description 3
- 229910052760 oxygen Inorganic materials 0.000 claims description 3
- 239000006096 absorbing agent Substances 0.000 claims description 2
- 229920001577 copolymer Polymers 0.000 description 14
- NIXOWILDQLNWCW-UHFFFAOYSA-N acrylic acid group Chemical group C(C=C)(=O)O NIXOWILDQLNWCW-UHFFFAOYSA-N 0.000 description 13
- OKKJLVBELUTLKV-UHFFFAOYSA-N Methanol Chemical compound OC OKKJLVBELUTLKV-UHFFFAOYSA-N 0.000 description 12
- 239000003999 initiator Substances 0.000 description 9
- 239000002904 solvent Substances 0.000 description 9
- XNLICIUVMPYHGG-UHFFFAOYSA-N pentan-2-one Chemical group CCCC(C)=O XNLICIUVMPYHGG-UHFFFAOYSA-N 0.000 description 8
- 239000000758 substrate Substances 0.000 description 6
- 239000007789 gas Substances 0.000 description 5
- CSCPPACGZOOCGX-UHFFFAOYSA-N Acetone Chemical compound CC(C)=O CSCPPACGZOOCGX-UHFFFAOYSA-N 0.000 description 4
- 239000003431 cross linking reagent Substances 0.000 description 4
- 239000008367 deionised water Substances 0.000 description 4
- 229910021641 deionized water Inorganic materials 0.000 description 4
- 230000036571 hydration Effects 0.000 description 4
- 238000006703 hydration reaction Methods 0.000 description 4
- 239000000203 mixture Substances 0.000 description 4
- YMWUJEATGCHHMB-UHFFFAOYSA-N Dichloromethane Chemical compound ClCCl YMWUJEATGCHHMB-UHFFFAOYSA-N 0.000 description 3
- 239000004743 Polypropylene Substances 0.000 description 3
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 description 3
- 239000008199 coating composition Substances 0.000 description 3
- 150000001875 compounds Chemical class 0.000 description 3
- 238000004132 cross linking Methods 0.000 description 3
- 239000012632 extractable Substances 0.000 description 3
- 239000000017 hydrogel Substances 0.000 description 3
- 239000010410 layer Substances 0.000 description 3
- 229920000642 polymer Polymers 0.000 description 3
- 239000003505 polymerization initiator Substances 0.000 description 3
- -1 polypropylene Polymers 0.000 description 3
- 229920001155 polypropylene Polymers 0.000 description 3
- 229910052710 silicon Inorganic materials 0.000 description 3
- 239000010703 silicon Substances 0.000 description 3
- 238000003618 dip coating Methods 0.000 description 2
- VFHVQBAGLAREND-UHFFFAOYSA-N diphenylphosphoryl-(2,4,6-trimethylphenyl)methanone Chemical compound CC1=CC(C)=CC(C)=C1C(=O)P(=O)(C=1C=CC=CC=1)C1=CC=CC=C1 VFHVQBAGLAREND-UHFFFAOYSA-N 0.000 description 2
- 238000001035 drying Methods 0.000 description 2
- 238000002513 implantation Methods 0.000 description 2
- 125000005395 methacrylic acid group Chemical group 0.000 description 2
- 229920003229 poly(methyl methacrylate) Polymers 0.000 description 2
- 239000004926 polymethyl methacrylate Substances 0.000 description 2
- 239000011877 solvent mixture Substances 0.000 description 2
- DGVVWUTYPXICAM-UHFFFAOYSA-N β‐Mercaptoethanol Chemical compound OCCS DGVVWUTYPXICAM-UHFFFAOYSA-N 0.000 description 2
- HJIAMFHSAAEUKR-UHFFFAOYSA-N (2-hydroxyphenyl)-phenylmethanone Chemical class OC1=CC=CC=C1C(=O)C1=CC=CC=C1 HJIAMFHSAAEUKR-UHFFFAOYSA-N 0.000 description 1
- NOBYOEQUFMGXBP-UHFFFAOYSA-N (4-tert-butylcyclohexyl) (4-tert-butylcyclohexyl)oxycarbonyloxy carbonate Chemical compound C1CC(C(C)(C)C)CCC1OC(=O)OOC(=O)OC1CCC(C(C)(C)C)CC1 NOBYOEQUFMGXBP-UHFFFAOYSA-N 0.000 description 1
- BQZJOQXSCSZQPS-UHFFFAOYSA-N 2-methoxy-1,2-diphenylethanone Chemical compound C=1C=CC=CC=1C(OC)C(=O)C1=CC=CC=C1 BQZJOQXSCSZQPS-UHFFFAOYSA-N 0.000 description 1
- RIWRBSMFKVOJMN-UHFFFAOYSA-N 2-methyl-1-phenylpropan-2-ol Chemical compound CC(C)(O)CC1=CC=CC=C1 RIWRBSMFKVOJMN-UHFFFAOYSA-N 0.000 description 1
- JHWGFJBTMHEZME-UHFFFAOYSA-N 4-prop-2-enoyloxybutyl prop-2-enoate Chemical compound C=CC(=O)OCCCCOC(=O)C=C JHWGFJBTMHEZME-UHFFFAOYSA-N 0.000 description 1
- NIXOWILDQLNWCW-UHFFFAOYSA-M Acrylate Chemical compound [O-]C(=O)C=C NIXOWILDQLNWCW-UHFFFAOYSA-M 0.000 description 1
- HNUALPPJLMYHDK-UHFFFAOYSA-N C[CH]C Chemical group C[CH]C HNUALPPJLMYHDK-UHFFFAOYSA-N 0.000 description 1
- MYMOFIZGZYHOMD-UHFFFAOYSA-N Dioxygen Chemical compound O=O MYMOFIZGZYHOMD-UHFFFAOYSA-N 0.000 description 1
- WHNWPMSKXPGLAX-UHFFFAOYSA-N N-Vinyl-2-pyrrolidone Chemical compound C=CN1CCCC1=O WHNWPMSKXPGLAX-UHFFFAOYSA-N 0.000 description 1
- HLJYBXJFKDDIBI-UHFFFAOYSA-N O=[PH2]C(=O)C1=CC=CC=C1 Chemical compound O=[PH2]C(=O)C1=CC=CC=C1 HLJYBXJFKDDIBI-UHFFFAOYSA-N 0.000 description 1
- CKIDCRFWPRVLEU-UHFFFAOYSA-N [3-(benzotriazol-2-yl)-4-hydroxyphenyl] prop-2-enoate Chemical class OC1=CC=C(OC(=O)C=C)C=C1N1N=C2C=CC=CC2=N1 CKIDCRFWPRVLEU-UHFFFAOYSA-N 0.000 description 1
- OCBFFGCSTGGPSQ-UHFFFAOYSA-N [CH2]CC Chemical group [CH2]CC OCBFFGCSTGGPSQ-UHFFFAOYSA-N 0.000 description 1
- 229920006243 acrylic copolymer Polymers 0.000 description 1
- 238000007605 air drying Methods 0.000 description 1
- 150000001298 alcohols Chemical class 0.000 description 1
- 125000001931 aliphatic group Chemical group 0.000 description 1
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 1
- BJFLSHMHTPAZHO-UHFFFAOYSA-N benzotriazole Chemical compound [CH]1C=CC=C2N=NN=C21 BJFLSHMHTPAZHO-UHFFFAOYSA-N 0.000 description 1
- 239000012964 benzotriazole Substances 0.000 description 1
- 238000005266 casting Methods 0.000 description 1
- 239000011247 coating layer Substances 0.000 description 1
- 230000000052 comparative effect Effects 0.000 description 1
- 238000010276 construction Methods 0.000 description 1
- 238000007796 conventional method Methods 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 229910001882 dioxygen Inorganic materials 0.000 description 1
- 238000009826 distribution Methods 0.000 description 1
- WNAHIZMDSQCWRP-UHFFFAOYSA-N dodecane-1-thiol Chemical compound CCCCCCCCCCCCS WNAHIZMDSQCWRP-UHFFFAOYSA-N 0.000 description 1
- QUPDWYMUPZLYJZ-UHFFFAOYSA-N ethyl Chemical group C[CH2] QUPDWYMUPZLYJZ-UHFFFAOYSA-N 0.000 description 1
- 238000002474 experimental method Methods 0.000 description 1
- 238000000605 extraction Methods 0.000 description 1
- 230000004907 flux Effects 0.000 description 1
- 125000000524 functional group Chemical group 0.000 description 1
- 229920001600 hydrophobic polymer Polymers 0.000 description 1
- 230000004410 intraocular pressure Effects 0.000 description 1
- 150000002576 ketones Chemical class 0.000 description 1
- 125000002496 methyl group Chemical group [H]C([H])([H])* 0.000 description 1
- 239000003960 organic solvent Substances 0.000 description 1
- 239000003791 organic solvent mixture Substances 0.000 description 1
- 238000000643 oven drying Methods 0.000 description 1
- 230000001590 oxidative effect Effects 0.000 description 1
- 239000001301 oxygen Substances 0.000 description 1
- 150000002978 peroxides Chemical class 0.000 description 1
- 239000002798 polar solvent Substances 0.000 description 1
- 229920002959 polymer blend Polymers 0.000 description 1
- 238000002360 preparation method Methods 0.000 description 1
- HNJBEVLQSNELDL-UHFFFAOYSA-N pyrrolidin-2-one Chemical compound O=C1CCCN1 HNJBEVLQSNELDL-UHFFFAOYSA-N 0.000 description 1
- 210000001525 retina Anatomy 0.000 description 1
- 239000002210 silicon-based material Substances 0.000 description 1
- 238000004528 spin coating Methods 0.000 description 1
- 230000008961 swelling Effects 0.000 description 1
- 238000009281 ultraviolet germicidal irradiation Methods 0.000 description 1
Classifications
-
- 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
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/28—Materials for coating prostheses
- A61L27/34—Macromolecular materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
- A61F2/16—Intraocular lenses
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
- A61F2/16—Intraocular lenses
- A61F2002/1696—Having structure for blocking or reducing amount of light transmitted, e.g. glare reduction
Landscapes
- Health & Medical Sciences (AREA)
- Public Health (AREA)
- Animal Behavior & Ethology (AREA)
- Veterinary Medicine (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Transplantation (AREA)
- General Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Medicinal Chemistry (AREA)
- Epidemiology (AREA)
- Chemical & Material Sciences (AREA)
- Ophthalmology & Optometry (AREA)
- Dermatology (AREA)
- Biomedical Technology (AREA)
- Engineering & Computer Science (AREA)
- Cardiology (AREA)
- Heart & Thoracic Surgery (AREA)
- Vascular Medicine (AREA)
- Materials For Medical Uses (AREA)
- Prostheses (AREA)
- Eyeglasses (AREA)
- Application Of Or Painting With Fluid Materials (AREA)
- Coating Of Shaped Articles Made Of Macromolecular Substances (AREA)
Description
Oppfinnelsens feltThe field of invention
Foreliggende oppfinnelse vedrører belegg for implanterbare oftalmiske linser. Spesielt vedrører den foreliggende oppfinnelse hydrofile belegg som appliseres på kanten av implanterbare oftalmiske linser. The present invention relates to coatings for implantable ophthalmic lenses. In particular, the present invention relates to hydrophilic coatings which are applied to the edge of implantable ophthalmic lenses.
Oppfinnelsens bakgrunnThe background of the invention
Både harde og myke implanterbare oftalmiske linsematerialer er kjent. Det vanligste harde materialet anvendt i oftalmiske implantater er polymetyl metakrylat ("PMMA"). Myke intraokkulære linse ("IOL")-materialer kan generelt deles i tre kategorier: silisium materialer, hydrogel materialer og ikke-hydrogel ("hydrofobe")(met)akryl materialer. Se for eksempel Foldable Intraocular Lenses, Ed. Martin et al., Slack Incorporated, Thorofare, New Jersey (1993). For for-mål innen foreliggende søknad er hydrofobe Both hard and soft implantable ophthalmic lens materials are known. The most common hard material used in ophthalmic implants is polymethyl methacrylate ("PMMA"). Soft intraocular lens ("IOL") materials can generally be divided into three categories: silicon materials, hydrogel materials, and non-hydrogel ("hydrophobic") (meth)acrylic materials. See, for example, Foldable Intraocular Lenses, Ed. Martin et al., Slack Incorporated, Thorofare, New Jersey (1993). For purposes within the present application are hydrophobic
(met)akrylmaterialer (met)akrylmaterialer som absorberer mindre enn omtrent 5 % vann ved romtemperatur. (meth)acrylic materials (meth)acrylic materials that absorb less than about 5% water at room temperature.
Som beskrevet i U.S.-patent nr. 5.755.786, kan IOLer, spesielt IOLer laget for implantasjon gjennom et lite inn-snitt, lide av et kantblendingsproblem. Oppfinnelsen beskrevet i '786-patentet reduserer kantblending ved å inkludere midler, slik som en pluralitet av v-formede for-dypninger, på den optiske kants overflate for å reflektere synlig lys som kontakter kantoverflaten vekk fra pasientens retina. As described in U.S. Patent No. 5,755,786, IOLs, particularly IOLs made for implantation through a small incision, can suffer from an edge glare problem. The invention described in the '786 patent reduces edge glare by including means, such as a plurality of v-shaped depressions, on the optical edge surface to reflect visible light contacting the edge surface away from the patient's retina.
Andre metoder for å redusere kantblending inkluderer de beskrevet i U.S. patent nr. 5.693.093; 5.769.889; 4.808.181; og 4.605.409. Other methods of reducing edge glare include those described in U.S. Pat. Patent No. 5,693,093; 5,769,889; 4,808,181; and 4,605,409.
Oppsummering av oppfinnelsenSummary of the invention
Den foreliggende oppfinnelse vedrører hydrofile belegg-sammensetninger for kirurgiske implantater, spesielt oftal miske implantater omfattende silisium- eller hydrofobe (met)akrylmaterialer. Mer spesielt vedrører den foreliggende oppfinnelse et beleggmateriale omfattende en oftalmisk akseptabel hydrofob (met)akrylpolymer og en oftalmisk akseptabel hydrofil polymer. The present invention relates to hydrophilic coating compositions for surgical implants, especially ophthalmic implants comprising silicon or hydrophobic (meth)acrylic materials. More particularly, the present invention relates to a coating material comprising an ophthalmically acceptable hydrophobic (meth)acrylic polymer and an ophthalmically acceptable hydrophilic polymer.
Den foreliggende oppfinnelse vedrører også en fremgangsmåte for å redusere kantblending i implanterbare oftalmiske linser. Fremgangsmåten omfatter å applisere et belegg omfattende en oftalmisk akseptabel hydrofob (met)akrylpolymer og en oftalmisk akseptabel hydrofil polymer på et implan-tats optiske kantoverflate. Når belegget er hydrert, er det uklart eller opakt og reduserer eller eliminerer kantblending. The present invention also relates to a method for reducing edge glare in implantable ophthalmic lenses. The method comprises applying a coating comprising an ophthalmically acceptable hydrophobic (meth)acrylic polymer and an ophthalmically acceptable hydrophilic polymer to an implant's optical edge surface. When the coating is hydrated, it is cloudy or opaque and reduces or eliminates edge glare.
Detaljert beskrivelse av oppfinnelsenDetailed description of the invention
Med mindre noe annet er indikert, er alle mengder uttrykket som % (w/w). Unless otherwise indicated, all amounts are expressed as % (w/w).
Som anvendt heri betyr hydrofob "(met)akrylpolymer"en hydrofob metakrylpolymer, en hydrofob akrylpolymer eller en hydrofob polymer inneholdende både metakryliske og akry-liske funksjonelle grupper. Som anvendt heri betyr "hydrofob" at materialene absorberer mindre enn omtrent 5 % vann ved romtemperatur. As used herein, hydrophobic "(meth)acrylic polymer" means a hydrophobic methacrylic polymer, a hydrophobic acrylic polymer, or a hydrophobic polymer containing both methacrylic and acrylic functional groups. As used herein, "hydrophobic" means that the materials absorb less than about 5% water at room temperature.
Beleggmaterialet av den foreliggende oppfinnelse omfatter en oftalmisk akseptabel hydrofob (met)akrylpolymer og en hydrofil polymer. Når beleggmaterialet er hydrert, har det en Tg mindre enn 37 °C, og fortrinnsvis mindre enn 15 °C. Den hydrofobe (met)akrylpolymer ingrediens i beleggmaterialet er fortrinnsvis klebrig for å bistå i anbring-elsen av beleggmaterialet på substratet. Mange oftalmisk akseptable hydrofobe (met)akrylpolymerer er kjent, inklusive de beskrevet i U.S. patent nr. 5.290.892; 5.693.095; og 5.331.073, hvis fullstendige innhold herved innlemmes ved referanse. Selv om alfatiske (met)akrylatmonomerer kan anvendes for å danne den hydrofobe (met)akrylpolymer, omfatter den hydrofobe (met)akrylatpolymer fortrinnsvis minst en (met)akrylmonomer som inneholder en aromatisk gruppe, slik som de materialer definert i US 5.693.095: The coating material of the present invention comprises an ophthalmically acceptable hydrophobic (meth)acrylic polymer and a hydrophilic polymer. When the coating material is hydrated, it has a Tg of less than 37°C, and preferably less than 15°C. The hydrophobic (meth)acrylic polymer ingredient in the coating material is preferably sticky to assist in the application of the coating material to the substrate. Many ophthalmically acceptable hydrophobic (meth)acrylic polymers are known, including those described in U.S. Pat. Patent No. 5,290,892; 5,693,095; and 5,331,073, the entire contents of which are hereby incorporated by reference. Although aliphatic (meth)acrylate monomers may be used to form the hydrophobic (meth)acrylic polymer, the hydrophobic (meth)acrylate polymer preferably comprises at least one (meth)acrylic monomer containing an aromatic group, such as the materials defined in US 5,693,095:
hvori: X er H eller CH3; wherein: X is H or CH3;
m er 0-6; m is 0-6;
Y er ingenting, O, S eller NR, hvori R er H, CH3, CnH2n+1(n=l-10) , iso-OC3H7, C6H5eller CH2C6HS; og Ar er enhver aromatisk ring som kan være usub-stituert eller substituert med CH3, C2H5, n-C3H7, iso-C3H7, OCH3, C6Hn, Cl, Br, C6HSeller CH2C6H5. Y is nothing, O, S or NR, wherein R is H, CH3, CnH2n+1(n=1-10), iso-OC3H7, C6H5 or CH2C6HS; and Ar is any aromatic ring which may be unsubstituted or substituted with CH3, C2H5, n-C3H7, iso-C3H7, OCH3, C6Hn, Cl, Br, C6HS or CH2C6H5.
Passende hydrofobe (met)akrylpolymerer inkluderer kopolymerer av 2-fenyletyl-metakrylat (2-PEMA) og 2-fenyletyl-akrylat (2-PEA). Suitable hydrophobic (meth)acrylic polymers include copolymers of 2-phenylethyl methacrylate (2-PEMA) and 2-phenylethyl acrylate (2-PEA).
Etter valg av (met)akrylmonomeren(e), dannes den hydrofobe (met)akrylpolymer ved å anvende en initiator (generelt ca. 2 % eller mindre). En hvilken som helst type polymerisa-sjonsinitiator kan anvendes, inklusive termiske initiatorer og fotoinitiatorer. En foretrukket initiator er benzoyl-fosfinoksidinitiatoren, 2,4,6-trimetyl-benzoyldifenylo-fosfinoksid ("TPO"), som kan aktiveres med blått lys eller UV-bestråling. Passende termiske initiatorer inkluderer de konvensjonelle peroksider t-butyl-peroktoat og bis-azoiso-butronitril. Passende UV-initiatorer inkluderer benzoin-metyleter, Darocur 1173 og Darocur 4265 UV-initiatorer. After selecting the (meth)acrylic monomer(s), the hydrophobic (meth)acrylic polymer is formed by using an initiator (generally about 2% or less). Any type of polymerization initiator can be used, including thermal initiators and photoinitiators. A preferred initiator is the benzoyl phosphine oxide initiator, 2,4,6-trimethyl-benzoyldiphenyl phosphine oxide ("TPO"), which can be activated by blue light or UV irradiation. Suitable thermal initiators include the conventional peroxides t-butyl-peroctoate and bis-azoiso-butronitrile. Suitable UV initiators include benzoin methyl ether, Darocur 1173 and Darocur 4265 UV initiators.
Den hydrofobe (met)akrylpolymer inneholder eventuelt en eller flere ingredienser valgt fra gruppen bestående av UV-absorbatorer som er kopolymeriserbare med de andre (met)akrylingredienser; blått lys-blokkerende fargestoffer som er kopolymeriserbare med de andre The hydrophobic (meth)acrylic polymer optionally contains one or more ingredients selected from the group consisting of UV absorbers which are copolymerizable with the other (meth)acrylic ingredients; blue light-blocking dyes that are copolymerizable with the others
(met)akrylingredienser; og kjedeoverføringsmidler for å minimalisere kryssbinding. (meth)acrylic ingredients; and chain transfer agents to minimize cross-linking.
Ultrafiolett absorberende kromoforer kan være en hver forbindelse som absorberer lys som har en bølgelengde kortere enn ca. 400 nm, men som ikke absorberer noen vesentlige mengder synlig lys. Passende kopolymeriserbare ultrafiolettabsorberende forbindelser er de substituerte 2-hydrok-sybenzofenoner brakt for dagen i U.S.-patent nr. 4.3 04.895 og de 2-hydroksy-5-akryloksyfenyl-2H-benzotriazoler brakt for dagen i U.S.-patent nr. 4.528.311. Den mest foretrukne ultrafiolettabsorberende forbindelse er 2-(3'-metallyl-2'-hydroksy-5'-metylfenyl)benzotriazol. Passende polymeriser-bare blått lys-blokkerende kromoforer inkluderer de brakt for dagen i U.S.-patent nr. 5.470.932. Hvis en blålys akti-vert polimerisasjonsinitiator velges og et blålysblokke-rende fargestoff tilsettes, kan polymerisasjonsinitiator-identiteten eller konsentrasjonen måtte justeres for å minimalisere noen interferens. Ultraviolet absorbing chromophores can be any compound that absorbs light having a wavelength shorter than about 400 nm, but which does not absorb any significant amounts of visible light. Suitable copolymerizable ultraviolet absorbing compounds are the substituted 2-hydroxybenzophenones disclosed in U.S. Patent No. 4,304,895 and the 2-hydroxy-5-acryloxyphenyl-2H-benzotriazoles disclosed in U.S. Patent No. 4,528,311. The most preferred ultraviolet absorbing compound is 2-(3'-methallyl-2'-hydroxy-5'-methylphenyl)benzotriazole. Suitable polymerizable blue light blocking chromophores include those disclosed in U.S. Patent No. 5,470,932. If a blue light activated polymerization initiator is selected and a blue light blocking dye is added, the polymerization initiator identity or concentration may need to be adjusted to minimize any interference.
Kjedeoverføringsmidler, hvis nærværende, tilsettes typisk i en mengde som strekker seg fra 0,01 til 0,4 %. Mange kjede-overf øringsmidler er kjent i faget. Eksempel på passende kjedeoverføringsmidler inkluderer 1-dodekantiol og 2-mer-kaptoetanol. Chain transfer agents, if present, are typically added in an amount ranging from 0.01 to 0.4%. Many chain transfer agents are known in the art. Examples of suitable chain transfer agents include 1-dodecanethiol and 2-mer-captoethanol.
Den hydrofile polymer inneholdt i beleggmaterialene av den foreliggende oppfinnelse kan være enhver oftalmisk akseptabel hydrofil polymer. Passende hydrofile polymerer inkluderer, men er ikke begrenset til polyhydroksyetyl-metakrylat (polyHEMA); polyakrylamid; polyglyseryl-metakrylat og polyvinyl-pyrrolidon (PVP). Den mest foretrukne hydrofile polymer er PVP. Disse hydrofile polymerer er kommersielt tilgjengelige eller kan lages ved å anvende kjente frem-gangsmåter og erholdes fortrinnsvis i en renset form for å minimalisere ekstraherbare materialer ved implantasjon av den belagte IOL. The hydrophilic polymer contained in the coating materials of the present invention may be any ophthalmically acceptable hydrophilic polymer. Suitable hydrophilic polymers include, but are not limited to, polyhydroxyethyl methacrylate (polyHEMA); polyacrylamide; polyglyceryl methacrylate and polyvinyl pyrrolidone (PVP). The most preferred hydrophilic polymer is PVP. These hydrophilic polymers are commercially available or can be made using known methods and are preferably obtained in a purified form to minimize extractable materials upon implantation of the coated IOL.
Den hydrofile polymer har fortrinnsvis en molekylvekt (vekt gjennomsnitt) i området 2.500-100.000. Det er viktig at den hydrofile polymers molekylvekt er stor nok og er til stede i hydrogelbeleggmaterialet i en tilstrekkelig mengde til å danne hydrofile domener som er i stand til å spre lys. Den hydrofile polymer bør ikke være for liten, ellers kan en betydelig mengde av den lekke ut av belegget etter at belegget er applisert på IOLen. Den hydrofile polymer bør ikke være for stor, ellers kan den påvirke intraokulært trykk i fall noe av polymeren lekker ut av belegget. I tilfelle med PVP er en molekylvekt på 10.000 foretrukket. The hydrophilic polymer preferably has a molecular weight (weight average) in the range 2,500-100,000. It is important that the molecular weight of the hydrophilic polymer is large enough and is present in the hydrogel coating material in a sufficient amount to form hydrophilic domains capable of scattering light. The hydrophilic polymer should not be too small, otherwise a significant amount of it may leak out of the coating after the coating is applied to the IOL. The hydrophilic polymer should not be too large, otherwise it may affect intraocular pressure if some of the polymer leaks out of the coating. In the case of PVP, a molecular weight of 10,000 is preferred.
Beleggmaterialet dannes ved å fremstille en oftalmisk akseptabel hydrofob (met)akrylpolymer, deretter rensing (om nødvendig eller ønsket) av den herdede hydrofobe (met)akrylpolymer via ekstraksjon i et passende løsnings-middel, deretter oppløsning av den hydrofobe (met)akrylpolymer og en oftalmisk akseptabel hydrofil polymer i et passende løsningsmiddel eller blanding av løs-ningsmidler for å danne en beleggløsning. Proporsjonen av hydrofob (met)akrylpolymer til hydrofil polymer i beleggsammensetningen avhenger av det ønskede hydratiserte vanninnhold for belegget, beleggets ønskede tykkelse, de valgte hydrofobe (met)akryl og hydrofile materialer, etc. Så snart den ønskede beleggtykkelse og vanninnhold er valgt, kan proporsjonen av hydrofob (met)akrylpolymer til hydrofilpolymer bestemmes ved rutineberegninger og eksperimen-tering. Generelt vil det ønskede vanninnhold av det hydratiserte belegg strekke seg fra ca. 20-70 % og den ønskede beleggtykkelse vil strekke seg fra 0,5-1 um. Typiske kon-sentrasjoner av hydrofilpolymer i beleggmaterialet vil derfor strekke seg fra ca. 5 til ca. 50 %, fortrinnsvis fra ca. 15 til ca. 30 %. The coating material is formed by preparing an ophthalmically acceptable hydrophobic (meth)acrylic polymer, then purifying (if necessary or desired) the cured hydrophobic (meth)acrylic polymer via extraction in a suitable solvent, then dissolving the hydrophobic (meth)acrylic polymer and a ophthalmically acceptable hydrophilic polymer in a suitable solvent or mixture of solvents to form a coating solution. The proportion of hydrophobic (meth)acrylic polymer to hydrophilic polymer in the coating composition depends on the desired hydrated water content of the coating, the desired thickness of the coating, the selected hydrophobic (meth)acrylic and hydrophilic materials, etc. Once the desired coating thickness and water content are selected, the proportion can of hydrophobic (meth)acrylic polymer to hydrophilic polymer is determined by routine calculations and experimentation. In general, the desired water content of the hydrated coating will range from approx. 20-70% and the desired coating thickness will range from 0.5-1 µm. Typical concentrations of hydrophilic polymer in the coating material will therefore range from approx. 5 to approx. 50%, preferably from approx. 15 to approx. 30%.
Løsningsmiddelet eller løsningsmiddelblandingen anvendt for å danne beleggløsningen bør velges for å gi en homogen be-leggløsning. Fordi beleggene vil anvendes for å redusere blending, er det ikke nødvendig for beleggløsningen å være klar. Enten beleggløsningen er klar eller ikke, bør belegget være gjennomskinnelig til opakt etter å ha blitt applisert på implantatets kant og hydratisert. Et eksempel på en passende løsningsmiddelblanding i tilfelle av en 2-PEMA/2-PEA-kopolymer som den hydrofobe (met)akrylpolymer og PRP som den hydrofile polymer er en 2-pentanon/metanol blanding. Generelt vil polare løsningsmidler slik som alkoholer være passende når den hydrofile polymer er polyHEMA eller polyglyserylmetakrylat, og ketoner, slik som 2-pentanon, eller metylenklorid, vil være passende når den hydrofile polymer er polyakrylamid eller PVP. The solvent or solvent mixture used to form the coating solution should be chosen to give a homogeneous coating solution. Because the coatings will be used to reduce glare, it is not necessary for the coating solution to be clear. Whether the coating solution is clear or not, the coating should be translucent to opaque after being applied to the edge of the implant and hydrated. An example of a suitable solvent mixture in the case of a 2-PEMA/2-PEA copolymer as the hydrophobic (meth)acrylic polymer and PRP as the hydrophilic polymer is a 2-pentanone/methanol mixture. In general, polar solvents such as alcohols will be suitable when the hydrophilic polymer is polyHEMA or polyglyceryl methacrylate, and ketones such as 2-pentanone or methylene chloride will be suitable when the hydrophilic polymer is polyacrylamide or PVP.
Beleggmaterialet er fortrinnsvis festet til substrat IOL ved hjelp av en eller begge de følgende: (1) hydrofob eller "fysisk" (dvs. ikke-kovalent) kryssbinding og (2) inter-penetrerende polymer nettoppbygging. Beleggmaterialet er i sitt indre kryssbundet med ikke-kovalent kryssbinding. Alternativt kan beleggmaterialet være kovalent kryssbundet til IOL ved hjelp av et kryssbindingsmiddel. The coating material is preferably attached to the substrate IOL by means of one or both of the following: (1) hydrophobic or "physical" (ie, non-covalent) cross-linking and (2) interpenetrating polymer network construction. The coating material is internally cross-linked with non-covalent cross-linking. Alternatively, the coating material may be covalently cross-linked to the IOL using a cross-linking agent.
Beleggløsningen appliseres på implantatets kantoverflate ved konvensjonelle teknikker, slik som spinn- eller dypp-beleggingsprosesser eller støping av et belegglag rundt en forhåndsdannet stav av det optiske materialet. Dyppbeleg-ging er foretrukket. Implantatet dyppes fortrinnsvis med en slik hastighet for å på denne måten minimalisere enhver svelling av implantatet forårsaket av løsningsmiddelet i beleggløsningen. The coating solution is applied to the edge surface of the implant by conventional techniques, such as spin or dip coating processes or casting a coating layer around a preformed rod of the optical material. Dip coating is preferred. The implant is preferably dipped at such a rate as to thereby minimize any swelling of the implant caused by the solvent in the coating solution.
Etter at belegget er applisert på implantatet tørkes belegget. En totrinns tørkeprosess er foretrukket. Først tilla-tes det belagte implantat å tørke i luft inntil mesteparten eller alt løsningsmiddelet har fordampet (generelt £ 15 minutter). Deretter ovnstørkes det belagte implantat ved hevet temperatur, ca. 40-100 °C, for å eliminere så mye som mulig av det gjenværende løsningsmiddel. En foretrukket tørkeprosess involverer lufttørking ved romtemperatur i 15 minutter, etterfulgt av ovnstørking ved 90 °C i ca. 20-6 0 minutter. Hvis et kovalent kryssbindingsmiddel tilsettes til beleggløsningen, tørkes belegget på en måte som full-stendig aktiverer kryssbindingsmiddelet. After the coating has been applied to the implant, the coating is dried. A two-stage drying process is preferred. First, the coated implant is allowed to dry in air until most or all of the solvent has evaporated (generally 15 minutes). The coated implant is then oven-dried at an elevated temperature, approx. 40-100 °C, to eliminate as much as possible of the remaining solvent. A preferred drying process involves air drying at room temperature for 15 minutes, followed by oven drying at 90 °C for approx. 20-60 minutes. If a covalent cross-linking agent is added to the coating solution, the coating is dried in a way that fully activates the cross-linking agent.
Belegget kan lett fjernes med et mangfold av organiske løs-ningsmidler eller løsningsmiddelblandinger, inklusive det samme løsningsmiddel anvendt som basisen i fremstillingen av beleggløsningen. Belegget kan imidlertid ikke fjernes av vann. The coating can be easily removed with a variety of organic solvents or solvent mixtures, including the same solvent used as the base in the preparation of the coating solution. However, the coating cannot be removed by water.
Implantater egnet for belegging med de hydrofile belegg av den foreliggende oppfinnelse er fortrinnsvis laget av hydrofobe (met)akrylmaterialer, men kan også være konst-ruert for silisium eller silisium-(met)akryl kopolymerer. Foretrukne hydrofobe (met)akrylmaterialer er de polymere materialer beskrevet i U.S.-patent nr. 5.290.892 og 5.693.095, hvis hele innhold herved innlemmes ved referanse. I tilfelle der implantatet er en IOL, kan beleggene i den foreliggende oppfinnelse anvendes sammen med substratmaterialer ment for anvendelse som en "hard" IOL (som innsettes i en utbrettet tilstand) eller en "sammen-leggbar" eller "myk" IOL (som innsettes i en foldet eller sammenpresset tilstand). Passende IOL-materialer for å bli belagt inkluderer de brakt for dagen i U.S.-patent nr. 5.693,095 eller 5.331.073. Som anvendt heri, inkluderer "implantater" kontaktlinser. Implants suitable for coating with the hydrophilic coatings of the present invention are preferably made of hydrophobic (meth)acrylic materials, but can also be constructed of silicon or silicon (meth)acrylic copolymers. Preferred hydrophobic (meth)acrylic materials are the polymeric materials described in U.S. Patent Nos. 5,290,892 and 5,693,095, the entire contents of which are hereby incorporated by reference. In the case where the implant is an IOL, the coatings of the present invention may be used with substrate materials intended for use as a "hard" IOL (inserted in an extended state) or a "collapsible" or "soft" IOL (inserted in a folded or compressed state). Suitable IOL materials to be coated include those disclosed in U.S. Patent Nos. 5,693,095 or 5,331,073. As used herein, "implants" include contact lenses.
Når kovalente kryssbindingsmidler anvendes, kan det være nødvendig eller ønskelig å preparere implantatets overflate som vil motta belegget ved å eksponere implantatets overflate for en reaktiv plasmagass før applisering av beleggløsningen. Passende reaktive plasmagasser inkluderer oksiderende gasser, slik som oksygengass. Et passende plasmakammer er P<2>CIM B-Series plasmakammer laget av Advanced Plasma Systems, Inc. Ved å anvende et slikt kammer inkluderer passende plasmaparametre: kraft = 400 W, plasmagass = oksygen; trykk av plasmagass = 225 mTorr; ekspone-ringstid =4-6 minutter. When covalent cross-linking agents are used, it may be necessary or desirable to prepare the surface of the implant that will receive the coating by exposing the surface of the implant to a reactive plasma gas before applying the coating solution. Suitable reactive plasma gases include oxidizing gases, such as oxygen gas. A suitable plasma chamber is the P<2>CIM B-Series plasma chamber made by Advanced Plasma Systems, Inc. Using such a chamber, suitable plasma parameters include: power = 400 W, plasma gas = oxygen; pressure of plasma gas = 225 mTorr; exposure time = 4-6 minutes.
De følgende eksempler er ment å være illustrative, men ikke begrensende. The following examples are intended to be illustrative, but not limiting.
Eksempel 1: Blanding av hydrofob (met)akryl polymer og hydrofil polymer. Example 1: Mixture of hydrophobic (meth)acrylic polymer and hydrophilic polymer.
En kopolymer av 2-PEMA (1,5 vektdeler) og 2-PEA (3,24 vektdeler) ble fremstilt ved å anvende Darocur 4265 (0,06 vektdeler) som en initiator. Kopolymeren ble herdet i polypropylenplateformer (10 mm x 20 mm x 0,9 mm) ved eksponering for blått lys i en time ved å anvende en Kulzer Palatray CU blålysenhet (12 - 14 mW/cm2) . Den herdede kopolymer (0,8345 A copolymer of 2-PEMA (1.5 parts by weight) and 2-PEA (3.24 parts by weight) was prepared using Darocur 4265 (0.06 parts by weight) as an initiator. The copolymer was cured in polypropylene sheet molds (10 mm x 20 mm x 0.9 mm) by exposure to blue light for one hour using a Kulzer Palatray CU blue light unit (12-14 mW/cm 2 ). The cured copolymer (0.8345
g) ble deretter ekstrahert i metanol ved romtemperatur natten over. Den ekstraherte kopolymer ble tørket i luft, men ikke strippet for metanolløsningsmiddel. Så snart de var tørre ble platene løst i en blanding av 2-pentanon og metanol for å danne den følgende beleggløsning: g) was then extracted in methanol at room temperature overnight. The extracted copolymer was dried in air but not stripped of methanol solvent. Once dry, the plates were dissolved in a mixture of 2-pentanone and methanol to form the following coating solution:
Separat ble en kopolymer omfattende 65 % 2-PEA; 30 % 2-PEMA; 1,8 % o-metallyl Tinuvin P; og 3,2 % 1,4-butandiol-diakrylat fremstilt ved å anvende 1,8 % Perkadox-16 som en termisk initiator. Denne kopolymer ("substrat kopolymer") ble herdet i de samme plateformer som beskrevet over og deretter ekstrahert i aceton (natten over, deretter tørket i luft i omtrent 2 timer, så tørket ved 100 °C i omtrent 2 timer). Dessuten ble kommersielt tilgjengelige ACRYSOF<*>IOL'er skaffet. Platene og IOL'ene ble deretter dyppet i beleggløsningen, tørket i luft i omtrent 5-10 minutter, og deretter ovnstørket i 90 °C i 20-90 minutter. Det herdede belegg var optisk klart. Etter hydrering av belegget er belegget gjennomskinnelig/opakt på grunn av den heterogene fordeling av vann innenfor beleggsammensetningen. Belegg-tykkelsen var typisk 0,5 til 1 mikron. Etter å ha vært hydrert i 9 måneder syntes beleggets uklarhet eller opasi-sitet ikke å ha minsket og forble bundet til substratplaten eller IOL. Separately, a copolymer comprising 65% 2-PEA; 30% 2-PEMA; 1.8% o-methallyl Tinuvin P; and 3.2% 1,4-butanediol diacrylate prepared using 1.8% Perkadox-16 as a thermal initiator. This copolymer ("substrate copolymer") was cured in the same plates described above and then extracted in acetone (overnight, then dried in air for about 2 hours, then dried at 100°C for about 2 hours). Also, commercially available ACRYSOF<*>IOLs were obtained. The plates and IOLs were then dipped in the coating solution, air dried for approximately 5-10 minutes, and then oven dried at 90°C for 20-90 minutes. The cured coating was optically clear. After hydration of the coating, the coating is translucent/opaque due to the heterogeneous distribution of water within the coating composition. The coating thickness was typically 0.5 to 1 micron. After being hydrated for 9 months, the haze or opacity of the coating did not appear to have decreased and remained bonded to the substrate plate or IOL.
Eksempel 2: Vanninnhold i beleggmaterialet fra eksempel 1. Example 2: Water content in the coating material from example 1.
For å bestemme vanninnholdet av det hydrerte beleggmaterialet anvendt i eksempel 1 ble en multilag film av be-leggløsningen definert i krav 1 støpt i en polypropylen-plateform. Etter at hvert lag var applisert ble det tillatt å tørke ved romtemperatur i luft før det neste lag ble tilsatt. Etter at fire eller 5 lag var laget ble multilag-filmen tørket ved 100 °C i en time. Den tørkede film ble veiet og deretter plassert i deionisert vann ved romtemperatur. Filmens vektendring ble overvåket over tid. Resul-tatene er vist i tabell 1 under. Etter 184 timers hydrering ble filmen fjernet fra det deioniserte vann, veiet, ekstrahert, tørket og veiet igjen. Filmen ga 5,7 % (basert på vekt) ekstraherbare materialer og hadde et vanninnhold (hydratisert) på 52,6 % (vekt). Filmen ble satt tilbake i det deioniserte vann i ytterligere 432 timer (616 timer total hydreringstid fra begynnelsen av eksperimentet). Det beregnede vanninnhold ved 616 timer var 59,5 % (vekt). In order to determine the water content of the hydrated coating material used in example 1, a multilayer film of the coating solution defined in claim 1 was cast in a polypropylene sheet mold. After each layer was applied, it was allowed to dry at room temperature in air before the next layer was added. After four or 5 layers were made, the multilayer film was dried at 100 °C for one hour. The dried film was weighed and then placed in deionized water at room temperature. The film's weight change was monitored over time. The results are shown in table 1 below. After 184 hours of hydration, the film was removed from the deionized water, weighed, extracted, dried and weighed again. The film yielded 5.7% (based on weight) extractables and had a water content (hydrated) of 52.6% (weight). The film was placed back into the deionized water for an additional 432 hours (616 hours total hydration time from the beginning of the experiment). The calculated water content at 616 hours was 59.5% (weight).
Eksempel 3: (Sammenligningseksempel) Kopolymer av hydrofobe (met)akrylmonomerer og hydrofil monomer. Example 3: (Comparative example) Copolymer of hydrophobic (meth)acrylic monomers and hydrophilic monomer.
Til 3,25 g 2-PEA ble 1,5 g 2-PEMA, 1,81 g N-vinylpyrrolidon og 0,06 g Darocur 4265 tilsatt. Pyrrolidon-innholdet av beleggmaterialet var det samme som det anvendt i beleggmaterialet i eksempel 1 [27,3 %: 0,33/(0,88+0,33) = 1,81/(3,25 + 1,5 + 1,81 + 0,06)]. Det resulterende beleggmateriale ble herdet i de samme polypropylenplateformer beskrevet i eksempel 1. En en times blått lys herding ble utført ved å anvende Palatray CU-enheten med en fluks på12-14mW/cm<2>. En resulterende kopolymer ble løst i 2-pentanon for å gi beleggløsning med et 6 vektprosent kopolymer innhold. To 3.25 g of 2-PEA, 1.5 g of 2-PEMA, 1.81 g of N-vinylpyrrolidone and 0.06 g of Darocur 4265 were added. The pyrrolidone content of the coating material was the same as that used in the coating material in Example 1 [27.3%: 0.33/(0.88+0.33) = 1.81/(3.25 + 1.5 + 1 .81 + 0.06)]. The resulting coating material was cured in the same polypropylene sheet molds described in Example 1. A one hour blue light cure was performed using the Palatray CU unit with a flux of 12-14mW/cm<2>. A resulting copolymer was dissolved in 2-pentanone to give coating solution with a 6% by weight copolymer content.
En forhåndsekstrahert (aceton) plate av substrat-kopolymeren fra eksempel 1 ble dyppet i beleggløsningen, lufttør-ket ved romtemperatur i 10 minutter og ovnsherdet ved 90 °C i 75 minutter. Den belagte plate ble plassert i deionisert vann og dens hydreringsegenskaper fulgt over tid. Resulta-tene er vist i tabell 2 under. A pre-extracted (acetone) plate of the substrate copolymer from Example 1 was dipped in the coating solution, air dried at room temperature for 10 minutes and oven cured at 90°C for 75 minutes. The coated plate was placed in deionized water and its hydration properties followed over time. The results are shown in table 2 below.
Vanninnhold etter 425 timer = 12,3 % (endelig hydratisert vekt - endelig tørket vekt)/endelig hydratisert vekt Vandige ekstraherbare materialer = 0,6 % Water content after 425 hours = 12.3% (final hydrated weight - final dried weight)/final hydrated weight Aqueous extractables = 0.6%
Som vist i tabell 1 og 2 ga eksempel 1 og 3 signifikant forskjellige resultater. Det hydratiserte PEMA-PVP-poly-merblandinsbeleggmaterialet er opakt og med høyt vanninnhold, mens den hydratiserte, vilkårlige PEMA-NVP-kopolymer er klar og har et lavere vannopptak. As shown in Tables 1 and 2, Examples 1 and 3 gave significantly different results. The hydrated PEMA-PVP polymer blend coating material is opaque and has a high water content, while the hydrated random PEMA-NVP copolymer is clear and has a lower water uptake.
Oppfinnelsen har blitt beskrevet med referanse til disse foretrukne utførelsesformer; imidlertid skal det forståes at den kan utformes i andre spesifikke former eller varia-sjoner derav uten å avvike fra dens ånd eller essensielle karakteristikker. Utførelsesformene beskrevet over er derfor ansett å være illustrative i alle henseender og ikke begrensende, rammen av oppfinnelsen er indikert av de ved-lagte krav heller enn av den foregående beskrivelse. The invention has been described with reference to these preferred embodiments; however, it is to be understood that it may be designed in other specific forms or variations thereof without departing from its spirit or essential characteristics. The embodiments described above are therefore considered to be illustrative in all respects and not limiting, the scope of the invention being indicated by the appended claims rather than by the preceding description.
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US20130178935A1 (en) * | 2012-01-11 | 2013-07-11 | Lara Henry | Polarized component ocular devices |
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US5698192A (en) * | 1996-09-25 | 1997-12-16 | University Of Florida | Ocular implants and methods for their manufacture |
US6169127B1 (en) * | 1996-08-30 | 2001-01-02 | Novartis Ag | Plasma-induced polymer coatings |
EP1001720B1 (en) * | 1997-08-07 | 2002-10-02 | Alcon Laboratories, Inc. | Intracorneal diffractive lens |
-
2000
- 2000-12-06 BR BR0016998-6A patent/BR0016998A/en not_active Application Discontinuation
- 2000-12-06 JP JP2001551524A patent/JP2003519538A/en not_active Withdrawn
- 2000-12-06 MX MXPA02006841A patent/MXPA02006841A/en unknown
- 2000-12-06 AU AU25758/01A patent/AU768090B2/en not_active Ceased
- 2000-12-06 CA CA002392593A patent/CA2392593A1/en not_active Abandoned
- 2000-12-06 KR KR1020027007899A patent/KR20020062357A/en not_active Application Discontinuation
- 2000-12-06 NZ NZ520117A patent/NZ520117A/en unknown
- 2000-12-06 CN CN00818360A patent/CN1423570A/en active Pending
- 2000-12-06 WO PCT/US2000/033102 patent/WO2001051103A1/en active IP Right Grant
- 2000-12-06 EP EP00989222A patent/EP1246652A1/en not_active Withdrawn
-
2001
- 2001-01-08 AR ARP010100072A patent/AR034844A1/en unknown
-
2002
- 2002-06-20 ZA ZA200204972A patent/ZA200204972B/en unknown
- 2002-07-11 NO NO20023343A patent/NO20023343L/en not_active Application Discontinuation
-
2003
- 2003-01-29 HK HK03100727.7A patent/HK1048957A1/en unknown
Also Published As
Publication number | Publication date |
---|---|
JP2003519538A (en) | 2003-06-24 |
AU768090B2 (en) | 2003-12-04 |
ZA200204972B (en) | 2003-06-20 |
NO20023343D0 (en) | 2002-07-11 |
NZ520117A (en) | 2003-02-28 |
HK1048957A1 (en) | 2003-04-25 |
WO2001051103A1 (en) | 2001-07-19 |
MXPA02006841A (en) | 2003-05-23 |
BR0016998A (en) | 2002-10-15 |
EP1246652A1 (en) | 2002-10-09 |
KR20020062357A (en) | 2002-07-25 |
CA2392593A1 (en) | 2001-07-19 |
CN1423570A (en) | 2003-06-11 |
AU2575801A (en) | 2001-07-24 |
AR034844A1 (en) | 2004-03-24 |
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