• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    A silicone contact lens coated in a hydrophilizing manner has a radial cross section of the inner surface (1) of the contact lens, the edge region contour of said cross section between a turning point (6) and the outer edge being convex (7). In order to produce it, a silicon precursor material is introduced between a female and a male mould and polymerized there, and the polymerized contact lens is released from the mould by means of a liquid which swells said contact lens and it is completed after a PECVD/CVD coating without edge processing.
    公开号:AU2013206388A1
    申请号:U2013206388
    申请日:2013-02-01
    公开日:2014-09-04
    发明作者:Martin Gorne；Thomas Kordick
    申请人:LENSWISTA AG；
    IPC主号:G02B1-04
    专利说明:
    - I Contact Lens [1] The present application relates to a "soft" contact lens with excellent wearing properties. [2] Conventional contact lenses, e. g. those known from the German utility model publication G 87 10 765 U1, have a radially inner part made of a harder material, and a radially outer part made of a softer material. The inner surface is entirely concave and the outer surface entirely convex, i.e. both surfaces have a positive Gaussian curvature. This known lens is not satisfactory with regard to its wearing comfort. [3] It is also known to apply a hydrophilic coating to a contact lens made of poly(methyl methacrylate), PMMA (US 5,080,924). Still, the wearing comfort of such lenses is not perceived as satisfactory. [4] The invention aims at providing a contact lens having good or even excellent wearing comfort, and a method for its manufacture. [5] This problem is solved by a contact lens made of silicone, wherein a radial cross section on the inner face has a rim region between a point of inflection and the outer edge in which the cross section contour is convex, in particular with a radius of between 0,1 and 10 mm. Because of this rim contour, the lens particularly readily slips onto the tear liquid film. [6] In embodiments, the contact lens has a surface layer made of a hydrophilic material auf, which further improves on the wearing comfort. [7] According to another aspect, the problem is solved by a process in which a silicone precursor material is brought in between a female and a male mold and is polymerised, and the polymerised contact lens is removed from the mold by means of a liquid swelling the contact lens and completed without edge cutting. Thereby the occurrance of a cutting edge, which might be perceived as irritating, is avoided. [8] In embodiments, the raw lens thus obtained is hydrophilized in a combined PECVD/CVD-process, whereby particularly thick coatings are achieved. [9] Further features of the invention are available from the subsequent description of embodiments in conjunction with the claims and the drawings. The invention is not limited to the described embodiments, but defined by the scope of the appended claims. In particular, individual features of embodiments of the invention may be realized in a different number or combination than in the examples explained hereunder. In the following explanation of embodiments reference is made to the appended drawings, which show: [10] Figure 1a a schematic cross-sectional view of a contact lens placed on the cornea of an eye, [11] Figure 1 b a schematic close-up view of a rim portion of the contact lies of Figure 1a, [12] Figure 2 an electron-microscopic image of the rim portion of the contact lens, [13] Figure 3 a fluorescence diagram indicating a surface coating, [14] Figure 4 a flow diagram for a manufacturing method of the contact lens according to the invention, and [15] Figure 5 a cross-sectional view of a molding apparatus suitable for the manufacturing according to Figure 4. [16] The general shape of a contact lens is shown in Figures 1 a and 1 b: The inner face 1 facing the cornea, which face, in use, floats on a film of tear liquid, is concave in its central part Z, namely rotationally symmetric-aspheric with a conus coefficient of about -0.1 to -0.5, thus somewhat elliptically pointed. In principle, this face also may deviate from the rotational symmetry if required by the physiological conditions. The outer face 2 of the lens is naturally convex with radius somewhat deviating from that of the inner face in magnitude, in order to provide the desired dioptric power. In the outer rim portion R, the curvatures or radii, respectively, deviate from the central values in the following manner: On the outer face, an annular part 4 with stronger (inward) curvature, thus smaller radius, is radially contiguous to the central portion. To this part, another may be outwards contiguous which is again less curved, conical (thus non-curved) or slightly outwardly (i.e. negatively) curved portion 5. In terms of magnitude, the curvature here is always less (i.e. the radius larger) than in the first mentioned transition region 4, i.e. the lens smoothly terminates. [17] The inner face 1 also has an annular region radially contiguous to the central region with the elliptical face, which, however, is less curved, thus more flattish, corresponding to a larger radius of curvature in this region. Herein, the radius of curvature in a sectional plane is meant, which plane contains the optical axis of the lens. The line formed by the inner face and the sectional plane forms a point of inflection 6, i.e. the - '-j curvature of the line first becomes zero and then positive. For the Gaussian surface curvature, this means a transition to negative values. To this region, the region 7 is contiguous, where the inner face of the contact lens approaches to the global tangential plane; here, the curvature in the main section perpendicular to the radial sectional plane is zero, so that the Gaussian surface curvature becomes zero and still further outside, in the immediate edge region, again transitions to positive values. [18] Between these two points (in the sectional plane) or lines (on the surface) of curvature inflection 6 und 7 there is a region in which the contact lens gradually lifts, when viewed radially from inner to outer region, from the cornea. This region is crucial for the wearing comfort. As recognized by the inventors, in this region there should neither be formed an overly sharp edge, which might interrupt the film of tear liquid present on the cornea or might even cut into the cornea; nor should the rim region have an outwardly pointed, protruding, strongly curved edge ("Skispitzen-Profifl), which might irritate the eyelid slipping onto it from outwards during blinking. Rather, the annular regions according to the invention, smoothly transitioning towards an outer edge free from any sharp edges, (see Figure 2) achieve an unperturbed floating of the contact lens onto the tear liquid film and at the same time enable an unperturbed slipping of the eyelid onto the contact lens. It was found that the radius of the inner face, i.e. the inverse curvature, along the radial sectional plane, is for example between 0,1 and 4 mm, or above 0,5 mm on the one hand or/and below 2 mm on the other hand. The radial extension of the negatively curved area region may be 1 pm to 1 mm, for example more than 10 pm on the one hand or/and below 100 pm on the other hand. The outer edge itself may include, instead of one acute angle 8, two obtuse angles, between which an approximately cylindrical outer rim region 9 extends for e.g. 10-30 pm as discernible from Figure 2. [19] In Figure 3, a fluorescence diagram of a surface coating is shown, as may be applied for hydrophilizing the per se hydrophobic silicone base material of the contact lens. The core part of the lens consists of poly(dimethylsiloxane) with a Shore-A hardness of 25. In this example, for the purpose of analysis an applied PAA-(poly acrylic acid) layer has been stained with the fluorescence dye Rhodamin 6G, and the depth extension of the fluorescence has been determined by confocal microscopy. As can be seen, the entire thickness (line width) of the PAA coating is several tens of pm. The lens thickness at the measurement position (line spacing) is 118 pm. The coating was made by PECVD followed by CVD. During the plasma coating phase the pressure ratio was changed from an initially prominent Argon excess (>10:1) towards a similarly prominent Argon deficiency (<1:1 0) near the end, at decreasing total pressure. This conditioning step was followed by an on-top-polymerisation of water-free acrylic acid from the vapour phase at its normal vapour pressure, without action of a plasma and without the presence of a noble gas. The initially plasma-enhanced provided layer had a thickness of 20-30 nm, i.e.
    - _r in the order of magnitude of about one part per thousand of the entire layer thickness. Such layers have optically as well as physiologically excellent properties due to the strong hydrophilicity. The contact angle of the applied layer in water is less than 100 and typically 2-50. The beneficial shape effects of the according to the invention are targeted supported by this treatment of the material. [20] In Figure 4, a flow diagram of a process according to the invention is shown. Initially, a female and a male mold are provided, and a precursor material for poly(dimethylsiloxane) is brought into female mold, closed with the male part, and polymerized at a temperature between 150C-1 600C for 12-720 min. S1 (molding). After the closing, the mold parts are rotated with respect to one another by 1800 or another angle sufficiently large (>200), as long as the reaction mixture is just viscous (over 1000 cP; typically ca. 4000 cP), so that excess silicone is reliably separated and displaced into the annular space between the mold parts. In this separation, the rim contour described above is created due to the effect of the surface energy, allowing the dispensing with an edge cutting step or other edge treatment creating a cutting edge (e.g. punching). For demolding, the contact lens is partially swollen with an alkane such as e.g. hexane or another nonpolar or little polar solvent S3, so that it releases S5 without mechanical action from the mold and the manufacturing parts. The dipole moment of the solvent should not be more than 0,2 Debye to this end. In support, an ultrasonic bath may be employed. The starting material may be a liquid 2-component silicone by NuSil with a DK-value of above 700 barrer. If desired, the lens is transferred after evaporating the solvent in a vacuum into a coating chamber and initially is cleaned with an Argon plasma (ca. 1 min) and prepared. Then, a phase S7 with a slight Argon excess 1:1 to 2:1 (partial pressure ratio) with respect to acrylic acid vapour follows, the latter obtained from water-free acrylic acid. Exemplary pressures are 0,03 Torr for Argon and 0,015 Torr for acrylic acid. This phase, which takes 10 to 90 min, is followed by an about ten-minute phase at closed Argon supply and further reduced acrylicacid pressure (ca. 0,1 mTorr). Then, the plasma generator is switched off, and the lens is exposed at room temperature to the saturation pressure of the acrylic acid, until a turbidity indicates the completion of the process (about 5 min). The contact lens is watered for 24 h in a hydrophilic liquid, for example in isotonic saline solution, to remove potential remainders of the coating agent, and is steam sterilized at above 1200C. [21] In Figure 5, a two-part mold is shown, which is suitable for carrying out the above described process. The lower, female part 10 initially accommodates the reaction mixture and is then closed with the upper, male part 12, wherein a space 11 filled with the reaction mixture remains between them. The lower part 10 has chamfers 13', 13" facilitating the fitting together and separating the mold parts 10 and 12. The annular space is indicated as 14.
    - '-I [22] From the proceedings of the process an irregularity of the outer results insofar as it deviates from an exact circle line, other than known e.g. from punched lens contours. Because also the cornea never has exactly regular contours, this deviation from an ideal shape not only is not detrimental, but even has beneficial effects on the wearing comfort. The amount of the irregularity may be quantified by assigning, by calculation, an ideally approximating circle line to the projection of the outer rim, according to the criterion of a minimum sum of the squared deviations. The, the average square deviation is a measure of the irregularity, and is at least 5000 pm 2 (converted to magnitudes: about 1 % of half the lens diameter), but in embodiments may be more than 1000 pm 2 or more than 10000 pm 2 . [23] The contact lenses formed according to the invention may be used as cover lenses, i.e. with or without refractive power for physically protecting the cornea from irritations. This may be useful as a flanking, itself non-therapeutic measure for a medicinal-therapeutic eye treatment. [24] In the subsequent claims, "mainly consisting" is understood as a mass proportion of more than 50 %, in particular of more than 90 % up to entirely. "Curvature" is in each case the inverse radius of curvature, i.e. the radius of the approaching circle, wherein the sign is positive for convex surfaces and is negative for concave surfaces. The Gaussian surface curvature is the product of the two principal curvatures, thus is negative when both the principal curvatures have different signs (saddle surface), and is zero when one or both principal curvatures are zero (e.g. cylinder and conus surface). [25] The skilled person will realize that deviations from the embodiments described above are possible without leaving the scope of protection of the appended claims.
    权利要求:
    Claims (20)
    [1] 1. A silicone contact lens, wherein a radial cross section of the contact lens on the inner face of the contact lens has a rim portion between a point of inflection and the outer edge in which the contour of the cross section is convex, characterized by a hydrophilizing surface coating, the water contact angle of which is below 100.
    [2] 2. The contact lens of claim 1, wherein the minimum radius of the convex contour of the cross section is 0,1 - 10 mm.
    [3] 3. The contact lens of claim 1 or 2, wherein the minimum radius of the convex contour of the cross section is above 0,5 mm.
    [4] 4. The contact lens of one of the preceding claims, wherein the hydrophilizing layer mainly consists of (meth)acrylic acid units.
    [5] 5. The contact lens of one of the preceding claims, wherein the hydrophilizing layer is thicker than 1 pm.
    [6] 6. The contact lens of one of the preceding claims, wherein the silicone is poly(dimethylsiloxane).
    [7] 7. The contact lens of one of the preceding claims, wherein the rim portion of the contact lens is 1 pm to 1 mm in width.
    [8] 8. The contact lens of claim 7, wherein the rim portion is 0,01 mm to 0,1 mm in width.
    [9] 9. The contact lens of one of the preceding claims, wherein the outer rim of the contact lens has an irregularity insofar as a circle line, ascribed to the outer rim according to the criterion of least mean square deviation, has an average square deviation of at least 5000 pm 2 .
    [10] 10. A process for the manufacture of a silicone contact lens, the radial cross-section of which on the inner face of the contact lens includes a rim portion between a point of inflection and the outer edge in which the contour of the cross-section is convex, in which process a female mold part and a male mold part are provided, and a silicone precursor material is brought in between the mold parts and is polymerized there, characterized in that - I the polymerized contact lens is released from the mold using a liquid swelling the contact lens, and is completed without generating a cutting edge and is then hydrophilized in a combined P ECVD/CVD-process.
    [11] 11. The process of claim 10, wherein the contact lens is coated with cross-linked (meth)acrylic acid units.
    [12] 12. The process of claim 10 or 11, wherein a first coating step occurs in a low-pressure plasma.
    [13] 13. The process of claim 12, wherein a subsequent coating step occurs in the gas phase without action of a plasma.
    [14] 14. The process of one of claims 10 to 13, wherein a non-polar solvent is employed for releasing the contact lens from the mold.
    [15] 15. The process of claim 14, wherein the dipole moment is less than 0,2 Debye.
    [16] 16. The process of one of claims 10 to 15, wherein the released contact lens is treated with a polar liquid, after coating where applicable.
    [17] 17. The process of claim 16, wherein the dipole moment of the polar liquid is more than 1 Debye.
    [18] 18. The process of one of claims 10 to 17, wherein the two mold parts are rotated with respect to one another while the reaction mixture is still liquid, in order to separate the portion of the reaction mixture intended for forming the contact lens from excess material.
    [19] 19. The process of one of claims 10 to 18, wherein the contact lens is the one of one of claims 1 to 9.
    [20] 20. Use of the contact lens of one of claims 1 to 9, or the contact lens manufactured according to the process of one of claims 10 to 19, as a cover lens for protecting the cornea.
    类似技术:
    公开号 | 公开日 | 专利标题
    AU2013206388B2|2015-08-27|Contact lens
    TWI243922B|2005-11-21|Contact lenses with microchannels
    GB2024450A|1980-01-09|Semi-scleral contact lenses and methods of making them
    US9878473B2|2018-01-30|Multilayer contact lens and production process therefor
    TW201514579A|2015-04-16|Contact lenses for refractive correction
    JP4909469B2|2012-04-04|Ophthalmic lens and manufacturing method thereof
    WO2009071312A3|2010-01-21|Keratoprosthesis
    WO2000043825A1|2000-07-27|Apertured contact lenses
    TW201228811A|2012-07-16|Mold for diffractive ophthalmic lens
    AU2013206389B2|2015-09-03|Contact lens
    WO2016144483A1|2016-09-15|Tear shaping for refractive correction
    JP2018054993A|2018-04-05|Corneal correction contact lens
    TW201431662A|2014-08-16|Contact lens
    WO2017160574A1|2017-09-21|Contact lens with flexible center and rigid periphery
    JP6155457B2|2017-07-05|Multilayer contact lens and manufacturing method thereof
    TW201432343A|2014-08-16|Contact lens
    CN210742631U|2020-06-12|Orthokeratology mirror with ultrahigh or ultralow K value of cornea
    CN109154724B|2020-12-25|Contact lens
    CN112584795A|2021-03-30|Artificial cornea
    TH55709B|2003-03-13|Coating composition and method to reduce edge luster in implantable intraocular lenses.
    同族专利:
    公开号 | 公开日
    IN2014DN07222A|2015-04-24|
    EP2985638A1|2016-02-17|
    EP2810107A1|2014-12-10|
    BR112013022754A2|2020-08-04|
    KR20140133830A|2014-11-20|
    JP5913430B2|2016-04-27|
    JP2014186340A|2014-10-02|
    US20150036100A1|2015-02-05|
    CN104204863A|2014-12-10|
    EP2613180A1|2013-07-10|
    ES2474572T3|2014-07-09|
    RU2014135280A|2016-03-20|
    SG11201404482PA|2014-10-30|
    PL2613180T3|2014-11-28|
    CN104204863B|2016-08-17|
    WO2013083855A1|2013-06-13|
    EP2985638B1|2018-01-10|
    JP2014510946A|2014-05-01|
    EP2613180B1|2014-03-26|
    AU2013206388B2|2015-08-27|
    ES2659021T3|2018-03-13|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    US4042652A|1974-03-28|1977-08-16|Agfa-Gevaert, A.G.|Method for the production of silicone elastomer-containing articles|
    FR2265516B1|1974-03-28|1978-09-22|Agfa Gevaert Ag||
    JPS6030529B2|1977-04-28|1985-07-17|Nippon Kontakuto Renzu Seizo Kk||
    US4285890A|1977-04-28|1981-08-25|Nippon Contact Lens Manufacturing Ltd.|Method for manufacturing silicone contact lenses|
    US4153641A|1977-07-25|1979-05-08|Bausch & Lomb Incorporated|Polysiloxane composition and contact lens|
    US4680149A|1986-05-19|1987-07-14|International Hydron Corporation|Mold and method for spin casting a precisely configured article|
    AU7466787A|1986-06-25|1988-01-07|International Paper Company|Microwave tray|
    DE8710765U1|1987-08-06|1987-09-24|Giefer, Guenter, 6056 Heusenstamm, De||
    US4955711A|1987-11-30|1990-09-11|Animalens, Inc.|Contact lenses for animals|
    US5080924A|1989-04-24|1992-01-14|Drexel University|Method of making biocompatible, surface modified materials|
    US5326584A|1989-04-24|1994-07-05|Drexel University|Biocompatible, surface modified materials and method of making the same|
    US5271875A|1991-09-12|1993-12-21|Bausch & Lomb Incorporated|Method for molding lenses|
    AT336307T|1995-12-08|2006-09-15|Novartis Pharma Gmbh|PLASMA-INDUCED POLYMER COATINGS|
    JPH11172149A|1997-10-09|1999-06-29|Kuraray Co Ltd|Polymer molding product with hydrophilic surface and its production|
    US6310116B1|1997-10-09|2001-10-30|Kuraray Co., Ltd.|Molded polymer article having a hydrophilic surface and process for producing the same|
    JPH11254461A|1998-03-05|1999-09-21|Seiko Epson Corp|Manufacture of contact lens|
    US20010036556A1|1998-10-20|2001-11-01|James S. Jen|Coatings for biomedical devices|
    JP4023013B2|1998-11-25|2007-12-19|株式会社日立グローバルストレージテクノロジーズ|Surface modifier, magnetic recording medium, and magnetic recording apparatus|
    US6444145B1|1999-09-03|2002-09-03|Johnson & Johnson Vision Products, Inc.|Molds for use in contact lens production|
    US6835410B2|2001-05-21|2004-12-28|Novartis Ag|Bottle-brush type coatings with entangled hydrophilic polymer|
    JP4738663B2|2001-08-07|2011-08-03|株式会社メニコン|Ophthalmic article manufacturing method and manufacturing apparatus|
    US20040075182A1|2002-04-10|2004-04-22|Stephane Gobron|Stackable contact lens molds|
    JP4045135B2|2002-07-03|2008-02-13|株式会社メニコン|Hydrous contact lens and method for producing the same|
    EP1789821B1|2004-08-27|2019-04-10|CooperVision International Holding Company, LP|Silicone hydrogel contact lenses|
    US7320587B2|2005-08-09|2008-01-22|Cooper Vision, Inc.|Contact lens molds and systems and methods for producing same|
    US7360890B2|2005-08-11|2008-04-22|Coopervision, Inc|Contact lenses and methods for reducing conjunctival pressure in contact lens wearers|
    MY148313A|2006-12-21|2013-03-29|Novartis Ag|Process for the coating of biomedical articles|
    WO2009091728A2|2008-01-14|2009-07-23|Coopervision International Holding Company, Lp|Polymerizable contact lens formulations and contact lenses obtained therefrom|
    JP2009186916A|2008-02-08|2009-08-20|Asahi Glass Co Ltd|Method of manufacturing display device panel|
    EP2490620A4|2009-10-23|2017-03-22|Forsight Labs, Llc|Conformable therapeutic shield for vision and pain|WO2015096875A1|2013-12-27|2015-07-02|Lenswista Ag|Method of coating lens surfaces|
    EP3044250A4|2013-09-10|2017-04-05|Colorado State University Research Foundation|Synthetic polymeric materials and devices thereof|
    US10139521B2|2016-04-20|2018-11-27|Coopervision International Holding Company, Lp|Silicone elastomer-hydrogel hybrid contact lenses|
    CN108885280A|2016-04-20|2018-11-23|库柏维景国际控股公司|The contact lenses that silicone elastomer-silicon hydrogel blendes together|
    US10139522B2|2016-04-20|2018-11-27|Coopervision International Holding Company, Lp|Silicone elastomer-silicone hydrogel hybrid contact lenses|
    法律状态:
    2015-12-17| MK25| Application lapsed reg. 22.2i(2) - failure to pay acceptance fee|
    优先权:
    申请号 | 申请日 | 专利标题
    EP12000649.9A|EP2613180B1|2012-02-01|2012-02-01|Silicon contact lens|
    EP12000649.9||2012-02-01||
    PCT/EP2013/000323|WO2013083855A1|2012-02-01|2013-02-01|Contact lens|
    [返回顶部]