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US20060167545A1 - Intraocular lens - Google Patents

Intraocular lens Download PDF

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Publication number
US20060167545A1
US20060167545A1 US10/559,376 US55937604A US2006167545A1 US 20060167545 A1 US20060167545 A1 US 20060167545A1 US 55937604 A US55937604 A US 55937604A US 2006167545 A1 US2006167545 A1 US 2006167545A1
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US
United States
Prior art keywords
lens
wave
wave front
intraocular lens
asphericity
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.)
Abandoned
Application number
US10/559,376
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English (en)
Inventor
Werner Fiala
Christine Kreiner
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
acritec AG Gesellschaft fur Ophthalmologische Produkte
Original Assignee
acritec AG Gesellschaft fur Ophthalmologische Produkte
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by acritec AG Gesellschaft fur Ophthalmologische Produkte filed Critical acritec AG Gesellschaft fur Ophthalmologische Produkte
Assigned to ACRI, TEC GESELLSCHAFT FUER OPHTHAL. PRODUKTE MBH reassignment ACRI, TEC GESELLSCHAFT FUER OPHTHAL. PRODUKTE MBH ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: FIALA, WERNER, KREINER, CHRISTINE
Publication of US20060167545A1 publication Critical patent/US20060167545A1/en
Assigned to *ACRI.TEC AG GESELLSCHAFT FUER OPHTHALMOLOGISCHE PRODUKTE reassignment *ACRI.TEC AG GESELLSCHAFT FUER OPHTHALMOLOGISCHE PRODUKTE CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: *ACRI.TEC GESELLSCHAFT FUER OPHTHALMOLOGISCHE PRODUKTE MBH
Priority to US12/484,282 priority Critical patent/US8066767B2/en
Abandoned legal-status Critical Current

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Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01M—TESTING STATIC OR DYNAMIC BALANCE OF MACHINES OR STRUCTURES; TESTING OF STRUCTURES OR APPARATUS, NOT OTHERWISE PROVIDED FOR
    • G01M11/00—Testing of optical apparatus; Testing structures by optical methods not otherwise provided for
    • G01M11/02—Testing optical properties
    • G01M11/0228—Testing optical properties by measuring refractive power
    • 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 or corneal implants; Artificial eyes
    • A61F2/16—Intraocular lenses
    • A61F2/1613—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • 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 or corneal implants; Artificial eyes
    • A61F2/16—Intraocular lenses
    • A61F2/1613—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • A61F2/1637—Correcting aberrations caused by inhomogeneities; correcting intrinsic aberrations, e.g. of the cornea, of the surface of the natural lens, aspheric, cylindrical, toric lenses
    • A61F2/164—Aspheric 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
    • A61F2240/00—Manufacturing or designing of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2240/001—Designing or manufacturing processes
    • A61F2240/008—Means for testing implantable prostheses

Definitions

  • the invention concerns an intraocular lens (IOL) and a method of determining the imaging properties of intraocular lenses.
  • IOL intraocular lens
  • Lenses of that kind are known.
  • the topology of conventional intraocular lenses generally involves spherical curved surfaces whose imaging properties however are not ideally suited to producing an image on the retina of the human eye.
  • Known methods of determining the imaging properties of intraocular lenses therefore presuppose basically spherically curved surfaces.
  • the object of the invention is to provide an intraocular lens whose imaging properties produce an image of improved quality on the retina.
  • a further object of the invention is to provide a method of determining the imaging properties of the intraocular lens, which method provides reliable results independently of the topological nature of the lens.
  • an intraocular lens with negative spherical aberration there is attained by an intraocular lens with negative spherical aberration.
  • Conventional, spherically curved intraocular lenses of positive refractive power have a positive spherical aberration, that is to say they refract an incoming wave with a plane wave front into an outgoing wave with an elliptically oblongly curved wave front.
  • the focus of such a lens is accordingly not punctiform.
  • the intraocular lens according to the invention is preferably of such a configuration that, in the environment of immersion medium, in particular the in vivo environment (refractive index 1.336) in the eye it refracts an incoming wave with an elliptically oblongly curved wave front into an outgoing wave with a wave front which is substantially spherical.
  • the imaging properties of the cornea of the eye, which is in front of the IOL are better taken into consideration and the effect is that more accurate focusing on the retina is possible.
  • Such imaging properties are preferably achieved by the refractive index and the curvature of the lens surfaces being so selected that the lens at the centre has a refractive power D of greater than or equal to +3.
  • the shape of the lens surface or wave front is shown in section for different asphericities in FIG. 1 .
  • equation (1) describes a parabola and if its value is less than ⁇ 1 it then describes a hyperbola.
  • the hyperbolic wave front of a wave produced from an incoming plane wave by the lens according to the invention has an asphericity (asph OUT ) of less than or equal to ⁇ 1.
  • the intraocular lens preferably has at least one convexly curved surface whose curvature is of an asphericity (asph L ) of less than or equal to ⁇ 1.
  • FIG. 1 shows a view of the curvature of a curve described by equation (1) for various asphericity values
  • FIG. 2 shows a diagram of the asphericity of an outgoing wave for various topographical asphericities of the cornea with a corneal refractive power at the centre of 40 dioptres
  • FIG. 3 shows a diagram of the asphericity of an outgoing wave for various topographical asphericities of the cornea with a corneal refractive power at the centre of 50 dioptres
  • FIG. 4 shows a diagram of the negative asphericity of the surface of a first embodiment of the IOL according to the invention for the conversion of a spherical wave into another spherical wave and the negative asphericity of an outgoing wave measured in air and in the immersion medium in each case in dependence on the refractive power of the lens,
  • FIG. 5 shows a diagram of the negative asphericity of the surface of a second embodiment of the IOL according to the invention for the conversion of an aspherical wave into a spherical wave and the negative asphericity of an outgoing wave measured in air and in the immersion medium in each case in dependence on the refractive power of the lens,
  • FIG. 6 is a diagrammatic view of a measuring apparatus for determining the waveform of the outgoing wave refracted by an IOL with incoming radiation of plane waves
  • FIG. 7 shows a diagrammatic cross-section through a third embodiment of the IOL according to the invention.
  • FIG. 8 shows the wave front of an outgoing wave from the IOL shown in FIG. 7 in comparison with an outgoing wave from a lens with spherical surfaces measured in air
  • FIG. 9 shows the wave front of an outgoing wave from the IOL shown in FIG. 7 in comparison with an outgoing wave from a lens with spherical surfaces measured in the immersion medium.
  • the cornea has a refractive index of about 1.37 topographically it essentially represents an aspheroidal dish. It has a negligibly slight influence on refraction of an incoming wave. Refraction of the incident light depends rather on the one hand on the curvature which is predetermined by the topography of the cornea but on the other hand on the refractive index of the immersion medium behind the cornea (aqueous humour). As is known, that has a refractive index of 1.336.
  • asph c ⁇ 0.26 ⁇ 0.18
  • topography of the cornea is characterised by its surface refractive power at the centre point, that is to say on the optical axis.
  • a range of 40 to 50 dioptres (dpt) is assumed for that purpose, whereby the range of the surface refractive power of the cornea, which actually occurs in nature and which in accordance with knowledge at the present time is at 43 dpt as an average value, is masked both towards higher and also lower values.
  • FIGS. 2 and 3 show the asphericity (asph IN ) of a wave refracted by the cornea or the immersion medium, on the incidence of a plane wave, that is to say a wave with a plane wave front, like for example light which is emitted by a point at an infinitely far distance. That depends on the topographical asphericity of the cornea and the spacing of the apex of the wave front from the apex of the cornea (abscissa value). The spacing between the centre of the intraocular lens and the front apex point of the cornea in the human eye, which is between a minimum of 3 mm and a maximum of 6 mm, is taken as the basis for the range of that value.
  • the asphericity of the refracted wave front asph IN impinging on the intraocular lens is between 0 and +11.4.
  • the cornea has a positive spherical aberration as it refracts the beams at the edge more greatly than those at the centre.
  • an IOL with negative spherical aberration is required in order to refract the aspherical wave coming from the cornea so as to achieve improved image formation on the retina of the eye.
  • the IOL according to the invention is so designed that, in the environment of immersion medium, an incoming wave with an elliptically oblongly curved wave front is refracted into an outgoing wave with a substantially spherical wave front, wherein the refractive power of the IOL is to be so selected in dependence on the eye of the patient that the centre of the outgoing waves is on the retina of the eye.
  • the IOL according to the invention can assume various configurations: in accordance with a first embodiment, at its centre, in the environment of the immersion medium, it has a refractive power D I of at least +3 dpt and the refractive power decreases towards the edge of the lens.
  • a refractive index of 1.46 a lens diameter of 6 mm and an axis-parallel edge thickness of 0.25 mm is assumed to apply.
  • the asphericity of the surfaces of the IOL depends on the central surface refractive power of the IOL in the immersion medium. The configuration is shown in the lower curve (open circles).
  • FIG. 4 shows the configuration of the negative asphericity of the wave front of the outgoing wave which is produced by a corresponding IOL in the immersion medium if the incoming wave has a plane wave front.
  • the upper curve in FIG. 4 shows the negative asphericity of the wave front of an outgoing wave which is produced by the same lens measured in air when a wave with a plane wave front is incident.
  • the wave front of a plane incoming wave refracted by such a lens is shown in the two curves thereabove, namely for measurement in air (open triangles) and measurement in the immersion medium (open squares).
  • topographical asphericities of the refractive surfaces of the intraocular lens according to the invention at any event assume negative values of less than ⁇ 1 and the surfaces are therefore always hyperbolic. That applies in particular also in the case of an IOL according to the invention which has only one convex surface.
  • the asphericity in the case of an IOL with only one hyperbolic-aspherical surface is in that case always greater than in the case of a symmetrical IOL.
  • the asphericity values shown in FIGS. 4 and 5 represent minimum values in that sense.
  • the asphericity of at least one of the refractive surfaces of the IOL according to the invention with a refractive power in the immersion medium of D I ⁇ +3 dpt, is less than ⁇ 1.
  • the topography of at least one of the refractive surfaces can always be described by a hyperboloid.
  • the hyperbolic wave front has an asphericity asph OUT ⁇ 5.
  • a conventional IOL with spherically curved surfaces in contrast has a positive spherical aberration, that is to say it refracts an incoming wave with a plane wave front into an outgoing wave with an elliptically oblongly curved wave front. That basically applies in regard to the positive refractive power of the lens, that is to say both in air and also in the immersion medium, insofar as the refractive index of the lens material is greater than that of the environment medium, with a refractive index of the lens material of 1.46 in particular therefore also in the immersion medium.
  • an IOL according to the first embodiment of the present invention can be distinguished from an intraocular lens according to the state of the art when it is illuminated with a plane wave. And more specifically suitable measurement can be effected in vitro in a standardised measuring structure and does not need to be implemented in the human eye.
  • An example of such a measuring structure is shown in FIG. 6 . It essentially corresponds to a structure 610 known from the ISO standard 11979-2, comprising an arrangement of optical elements for producing a plane wave, that is to say for producing and collimating a parallel beam with which an IOL 614 to be measured is illuminated.
  • a wave front analyser in accordance with Hartmann-Shack 620, for determining the waveform of the outgoing wave produced by the IOL 614.
  • the wave front analyser breaks down the beam 616 coming from the IOL by means of a lens arrangement 622 into a plurality of beams 624 whose local distribution is detected by means of a light detector 626 , such as for example a CCD camera.
  • a light detector 626 such as for example a CCD camera.
  • the refraction properties for intraocular lenses are selected with refractive powers in the range between 3 dpt and 35 dpt.
  • the intraocular lenses according to the invention are not limited to those refractive powers. Higher refractive powers can equally be selected and can be easily extrapolated on the basis of the steady configuration of the curves.
  • the foregoing considerations were by way of example in respect of an IOL with a refractive index of 1.46, a diameter of 6 mm and an axis-parallel edge thickness of 0.25 mm.
  • the invention however is not limited to an IOL with the stated values for the refractive index, diameter or edge thickness.
  • the IOL in accordance with a second embodiment of the present invention has a central refractive power in the immersion medium D I of a maximum of ⁇ 2 dpt.
  • Such an IOL according to the invention also refracts an incoming wave with an elliptically oblongly curved wave front into an outgoing spherical wave, with suitable curvature for the lens surface, that is to say with a refractive power which decreases towards the lens edge (negative spherical aberration).
  • Such a lens according to the invention converts an incoming plane wave into an outgoing wave with an elliptically oblongly curved wave front.
  • a conventional spherical lens of positive refractive power converts an incoming plane wave into a wave with an elliptically oblongly curved wave front, that is to say the refracted edge beams experience greater deflection than the central beams.
  • spherical lenses with a positive refractive power have a positive spherical aberration. Accordingly, aberration is negative in the case of a spherical lens with negative refractive power.
  • Such a lens converts an incoming plane wave into an outgoing wave with an also elliptically oblongly curved wave front.
  • the wave fronts measured in the immersion medium, in investigation of the IOL according to the invention have a positive asphericity which is 1600 to 20 times greater in comparison with a conventional spherical IOL, in each case in dependence on the refractive power of the lenses.
  • the wave fronts produced by the IOL according to the invention in comparison with the wave fronts produced by a conventional spherical lens, have a positive asphericity which is increased by 500 to 8.5 times, once again dependent in each case on the refractive power of the lenses.
  • the asphericity of a spherical IOL with negative refractive power in air does not reach any values which are greater than +10.
  • the two outgoing waves can therefore be easily distinguished by measurement of their asphericity.
  • the refractive power of the lenses being known therefore once again it is possible by means of the apparatus shown in FIG. 6 to distinguish whether the lens being investigated is a conventional spherical IOL organ IOL according to the invention.
  • An intraocular lens according to a third embodiment of the present invention has a central refractive power of between +2 dpt and ⁇ 1 dpt in the immersion medium.
  • the refractive power of the IOL according to the invention is lower at the edge than at the centre.
  • FIG. 7 shows by way of example a symmetrical IOL 700 with a refractive power at the centre of +2 dpt, in cross-section.
  • FIGS. 8 and 9 show the configuration of the wave fronts of outgoing waves, which are produced by the IOL according to the invention on the one hand and a spherical IOL with the same nominal refractive power on the other hand, when a plane wave is introduced. It can be seen in the comparison that the meridian of the wave front produced by the IOL according to the invention has an inflexion point whereas the wave front produced by a conventional lens extends monotonically. That applies both in the environment medium air, see FIG. 8 , and also in the immersion medium, see FIG. 9 . In that way it is also possible to clearly distinguish lenses according to the invention with the above-mentioned refractive power from conventional, spherically curved lenses, by the method described with reference to FIG. 6 .

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  • Health & Medical Sciences (AREA)
  • Ophthalmology & Optometry (AREA)
  • Transplantation (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Physics & Mathematics (AREA)
  • Analytical Chemistry (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Chemical & Material Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • General Physics & Mathematics (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Prostheses (AREA)
US10/559,376 2003-06-06 2004-06-04 Intraocular lens Abandoned US20060167545A1 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
US12/484,282 US8066767B2 (en) 2003-06-06 2009-06-15 Intraocular lens

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
DE10325841.8 2003-06-06
DE10325841A DE10325841A1 (de) 2003-06-06 2003-06-06 Intraokularlinse
PCT/EP2004/006074 WO2004108017A1 (de) 2003-06-06 2004-06-04 Intraokularlinse

Related Parent Applications (1)

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PCT/EP2004/006074 A-371-Of-International WO2004108017A1 (de) 2003-06-06 2004-06-04 Intraokularlinse

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US12/484,282 Continuation US8066767B2 (en) 2003-06-06 2009-06-15 Intraocular lens

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US20060167545A1 true US20060167545A1 (en) 2006-07-27

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US12/484,282 Expired - Lifetime US8066767B2 (en) 2003-06-06 2009-06-15 Intraocular lens

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US (2) US20060167545A1 (de)
EP (1) EP1635740A1 (de)
JP (1) JP2006527014A (de)
KR (2) KR100866442B1 (de)
CA (1) CA2528024C (de)
DE (1) DE10325841A1 (de)
WO (1) WO2004108017A1 (de)

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070268453A1 (en) * 2006-05-17 2007-11-22 Alcon Manufacturing, Ltd. Correction of higher order aberrations in intraocular lenses
US20090132041A1 (en) * 2005-06-22 2009-05-21 Arc.Tec Ag Gesellschaft Fur Ophthalmologische Produkte Astigmatic intraocular lens
US20090157179A1 (en) * 2007-12-11 2009-06-18 Pinto Candido D Ophthalmic Lenses Providing an Extended Depth of Field
US8331048B1 (en) 2009-12-18 2012-12-11 Bausch & Lomb Incorporated Methods of designing lenses having selected depths of field
US20160256048A1 (en) * 2005-06-30 2016-09-08 Amo Manufacturing Usa, Llc Presbyopia correction through negative spherical aberration
US10485655B2 (en) 2014-09-09 2019-11-26 Staar Surgical Company Ophthalmic implants with extended depth of field and enhanced distance visual acuity
US10774164B2 (en) 2018-08-17 2020-09-15 Staar Surgical Company Polymeric composition exhibiting nanogradient of refractive index
US10881504B2 (en) 2016-03-09 2021-01-05 Staar Surgical Company Ophthalmic implants with extended depth of field and enhanced distance visual acuity
US12127934B2 (en) 2014-09-09 2024-10-29 Staar Surgical Company Method of Providing Modified Monovision to a Subject with a First Lens and a Second Lens
US12295829B2 (en) 2021-10-04 2025-05-13 Staar Surgical Company Ophthalmic implants for correcting vision with a tunable optic, and methods of manufacture and use

Families Citing this family (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2640315B1 (de) * 2010-11-15 2018-01-10 Elenza, Inc. Adaptive intraokularlinse
TWI588560B (zh) 2012-04-05 2017-06-21 布萊恩荷登視覺協會 用於屈光不正之鏡片、裝置、方法及系統
US9201250B2 (en) 2012-10-17 2015-12-01 Brien Holden Vision Institute Lenses, devices, methods and systems for refractive error
WO2014059465A1 (en) 2012-10-17 2014-04-24 Brien Holden Vision Institute Lenses, devices, methods and systems for refractive error
WO2019067033A2 (en) * 2017-06-15 2019-04-04 Analog Photonics LLC INTEGRATED OPTICAL STRUCTURES FOR LIDAR AND OTHER APPLICATIONS EMPLOYING MULTIPLE DETECTORS

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US5796462A (en) * 1995-05-04 1998-08-18 Johnson & Johnson Vision Products, Inc. Aspheric toric lens designs
US20010051826A1 (en) * 2000-02-24 2001-12-13 Bogaert Theo T. M. Intraocular lenses
US20020154271A1 (en) * 2000-02-16 2002-10-24 Christof Donitzky Method for producing an artificial ocular lense
US6533416B1 (en) * 2001-07-20 2003-03-18 Ocular Sciences, Inc. Contact or intraocular lens and method for its preparation

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JPH10507825A (ja) * 1994-06-14 1998-07-28 ヴィジョニクス・リミテッド 光要素をマッピングするための装置
US6609793B2 (en) * 2000-05-23 2003-08-26 Pharmacia Groningen Bv Methods of obtaining ophthalmic lenses providing the eye with reduced aberrations
SK16532002A3 (sk) * 2000-05-23 2003-07-01 Pharmacia Groningen Bv Spôsob získavania očných šošoviek poskytujúcich oku znížené aberácie

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US4504982A (en) * 1982-08-05 1985-03-19 Optical Radiation Corporation Aspheric intraocular lens
US5796462A (en) * 1995-05-04 1998-08-18 Johnson & Johnson Vision Products, Inc. Aspheric toric lens designs
US20020154271A1 (en) * 2000-02-16 2002-10-24 Christof Donitzky Method for producing an artificial ocular lense
US20010051826A1 (en) * 2000-02-24 2001-12-13 Bogaert Theo T. M. Intraocular lenses
US6533416B1 (en) * 2001-07-20 2003-03-18 Ocular Sciences, Inc. Contact or intraocular lens and method for its preparation

Cited By (18)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8465543B2 (en) 2005-06-22 2013-06-18 Carl Zeiss Meditec Ag Astigmatic intraocular lens
US20090132041A1 (en) * 2005-06-22 2009-05-21 Arc.Tec Ag Gesellschaft Fur Ophthalmologische Produkte Astigmatic intraocular lens
US10213102B2 (en) * 2005-06-30 2019-02-26 Amo Manufacturing Usa, Llc Presbyopia correction through negative spherical aberration
US20160256048A1 (en) * 2005-06-30 2016-09-08 Amo Manufacturing Usa, Llc Presbyopia correction through negative spherical aberration
US8852273B2 (en) 2006-05-17 2014-10-07 Novartis Ag Correction of higher order aberrations in intraocular lenses
US8211172B2 (en) 2006-05-17 2012-07-03 Novartis Ag Correction of higher order aberrations in intraocular lenses
US20110085133A1 (en) * 2006-05-17 2011-04-14 Xin Hong Correction of higher order aberrations in intraocular lenses
US20070268453A1 (en) * 2006-05-17 2007-11-22 Alcon Manufacturing, Ltd. Correction of higher order aberrations in intraocular lenses
US7879089B2 (en) 2006-05-17 2011-02-01 Alcon, Inc. Correction of higher order aberrations in intraocular lenses
US20090157179A1 (en) * 2007-12-11 2009-06-18 Pinto Candido D Ophthalmic Lenses Providing an Extended Depth of Field
US8331048B1 (en) 2009-12-18 2012-12-11 Bausch & Lomb Incorporated Methods of designing lenses having selected depths of field
US10485655B2 (en) 2014-09-09 2019-11-26 Staar Surgical Company Ophthalmic implants with extended depth of field and enhanced distance visual acuity
US12127934B2 (en) 2014-09-09 2024-10-29 Staar Surgical Company Method of Providing Modified Monovision to a Subject with a First Lens and a Second Lens
US12232952B2 (en) 2014-09-09 2025-02-25 Staar Surgical Company Ophthalmic implants with extended depth of field and enhanced distance visual acuity
US10881504B2 (en) 2016-03-09 2021-01-05 Staar Surgical Company Ophthalmic implants with extended depth of field and enhanced distance visual acuity
US10774164B2 (en) 2018-08-17 2020-09-15 Staar Surgical Company Polymeric composition exhibiting nanogradient of refractive index
US11427665B2 (en) 2018-08-17 2022-08-30 Staar Surgical Company Polymeric composition exhibiting nanogradient of refractive index
US12295829B2 (en) 2021-10-04 2025-05-13 Staar Surgical Company Ophthalmic implants for correcting vision with a tunable optic, and methods of manufacture and use

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JP2006527014A (ja) 2006-11-30
WO2004108017A1 (de) 2004-12-16
CA2528024C (en) 2012-07-31
CA2528024A1 (en) 2004-12-16
KR100866442B1 (ko) 2008-10-31
KR20060037263A (ko) 2006-05-03
US20090270983A1 (en) 2009-10-29
EP1635740A1 (de) 2006-03-22
DE10325841A1 (de) 2004-12-30
US8066767B2 (en) 2011-11-29
KR20070097132A (ko) 2007-10-02

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