EP1635740A1 - Lentille intraoculaire - Google Patents

Lentille intraoculaire

Info

Publication number
EP1635740A1
EP1635740A1 EP04736052A EP04736052A EP1635740A1 EP 1635740 A1 EP1635740 A1 EP 1635740A1 EP 04736052 A EP04736052 A EP 04736052A EP 04736052 A EP04736052 A EP 04736052A EP 1635740 A1 EP1635740 A1 EP 1635740A1
Authority
EP
European Patent Office
Prior art keywords
wave
lens
intraocular lens
wavefront
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.)
Withdrawn
Application number
EP04736052A
Other languages
German (de)
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.)
Carl Zeiss Meditec AG
Original Assignee
Acri Tec GmbH
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 Acri Tec GmbH filed Critical Acri Tec GmbH
Publication of EP1635740A1 publication Critical patent/EP1635740A1/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • 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
    • 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
    • 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, corneal implants; Implanting instruments specially adapted therefor; 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 relates to an intraocular lens (IO) and a method for determining the imaging properties of intraocular lenses.
  • IO intraocular lens
  • Such lenses are known.
  • the topology of conventional intraocular lenses generally has spherical curved surfaces, the imaging properties of which, however, are not ideally adapted for imaging on the retina of the human eye.
  • Known methods for determining the imaging properties of intraocular lenses therefore generally require a spherically curved surface
  • the object of the invention is to provide an intraocular lens whose imaging properties produce an image with improved quality on the retina.
  • the object of the invention is also to create a method for determining the imaging properties of the intraocular lens which delivers reliable results regardless of the topological nature of the lens.
  • the object is achieved according to the invention by an intraocular lens with negative spherical aberration.
  • Conventional, spherically curved intraocular lenses of positive refractive power have a positive spherical aberration, ie they break an incident wave with a flat wavefront into an outgoing wave with an elliptically oblong curved wavefront.
  • the focus of such a lens is therefore not point-like.
  • the intraocular lens according to the invention is preferably designed in such a way that it the immersion medium, especially the invivo environment (refractive index 1.336) in the eye breaks an incident wave with an elliptically oblong curved wavefront into an outgoing wave with an essentially spherical wavefront.
  • Such imaging properties are preferably achieved in that the refractive index and the curvature of the lens surfaces are selected such that the lens in the center has a refractive power D greater than or equal to +3 dioptrine (dpt) in the immersion medium, and that an incident wave in the vicinity of air with an essentially flat wavefront into an outgoing wave with a hyperbolic wavefront.
  • D refractive power
  • dpt +3 dioptrine
  • x coincides with the direction of light propagation or lens thickness
  • y indicates the direction perpendicular thereto, radially outwards with respect to the lens center
  • p is an arbitrary parameter
  • asph is the so-called asphericity, i.e. a measure of the deviation of the curvature of the lens surface from a spherical shape.
  • the lens surface or wavefront is shown in section for different asphericities in FIG. 1.
  • the equation accordingly describes an ellipse whose main axis in the x-direction (shown stretched) is smaller than that in the y-direction (oblong). is which is in the y direction (oblong). If the asphericity is 0, a circle is written. If it lies between 0 and -1 (in each case excluding the limit values), an ellipse is described whose main axis in the x direction is larger than that in the y direction (prolong). If the asphericity is -1, equation (1) describes a parabola, and if its value is less than -1, then it describes a hyperbola.
  • the hyperbolic wavefront of a wave generated from an incident plane wave by the lens according to the invention preferably has an asphericity (asph 0 tj ⁇ ) less than or equal to -5.
  • the intraocular lens also preferably has at least one convexly curved surface, the curvature of which has an asphericity (asph L ) less than or equal to -1.
  • Fig. 2 is a diagram of the asphericity of an outgoing
  • Fig. 3 is a diagram of the asphericity of an outgoing
  • FIG. 5 shows a diagram of the negative asphericity of the surface before a second exemplary embodiment of the IOL according to the invention for converting 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 as a function of the refractive power of the lens;
  • FIG. 6 shows a schematic representation of a measuring device for determining the waveform of the outgoing wave broken by an IOL when plane waves are irradiated
  • FIG. 7 shows a schematic cross section of a third exemplary embodiment of the IOL according to the invention.
  • FIG. 8 shows the wave front of a wave emanating from the IOL according to FIG. 7 compared to a wave emanating from a lens with spherical surfaces, measured in air;
  • FIG. 9 shows the wave front of a wave emanating from the IOL according to FIG. 7 in comparison to a wave emanating from a lens with spherical surfaces measured in the immersion medium.
  • the imaging ratios in the human eye taken into account in the IOL according to the invention are examined below.
  • the cornea has a refractive index of approximately 1.37 and, topographically, essentially represents an aspheroid shell. This has a negligible influence on the refraction of an incident wave.
  • the refraction of the incident light depends on the one hand on the curvature given by the topography of the cornea and on the other hand on the refractive index of the one behind the cornea
  • Immersion medium aqueous humor
  • aqueous humor This is known to have a refractive index of 1.336.
  • the topography of the cornea is characterized by its refractive power at the center, ie on the optical axis.
  • an interval of 40 to 50 diopters (dpt) is assumed, which covers the range of the surface power of the cornea that actually occurs in nature, which according to current knowledge is 43 dpt, both to higher and to lower values.
  • dpt diopters
  • FIGS. 2 and 3 the asphericity (asph IN ) of a wave broken by the cornea or the immersion medium upon the incidence of a plane wave, ie a wave with a plane wave front, such as light, which is emitted from an infinitely distant point, shown.
  • absa value This depends on the topographical asphericity of the cornea and on the distance from the apex of the wavefront to the apex of the cornea (abscissa value).
  • the interval of this value is based on the distance between the center of the intraocular lens and the front vertex of the cornea in the human eye, which is between a minimum of 3 mm and a maximum of 6 mm. 2 shows the conditions in the case of a cornea with a central surface power of 40 dpt.
  • the asphericity of the broken, on the intraocular lens impinging wavefront asph ⁇ N is between 0 and +11.4.
  • the cornea has a positive spherical aberration because it breaks the rays at the edge more than those in the center.
  • an IOL with negative spherical aberration is required to break the aspherical wave coming from the cornea, so that an improved image is achieved on the retina of the eye.
  • the IOL according to the invention is preferably designed such that an incident wave with an elliptically oblong curved wavefront is broken into an outgoing wave with an essentially spherical wavefront in the vicinity of the immersion medium, the refractive power of the IOL being chosen depending on the patient's eye that the center of the emerging waves lies on the retina of the eye.
  • the IOL according to the invention can take various forms: according to a first embodiment, it has a refractive power Di of at least +3 D in its center, in the vicinity of the immersion medium, and the refractive power decreases towards the edge of the lens. Furthermore, a refractive index of 1.46, a diameter of the lens of 6 mm and an axis-parallel edge thickness of 0.25 mm are assumed as examples.
  • the asphericity of the surfaces of the IOL depends on the central surface power of the IOL in the immersion medium. The course is shown in the lower curve (open circles).
  • Fig. 4 shows the course of the negative asphericity of the wave front of the outgoing wave, which is generated by a corresponding IOL in the immersion medium when the incident wave has a flat wave front.
  • the upper curve in Fig. 4 shows the negative asphericity of the wave front of an outgoing wave, which is measured by the same lens and is generated in air when a wave with a plane wave front is incident.
  • the wave front of a plane incident wave broken by such a lens is shown in the two curves above, namely for measurement in air (open triangles) and measurement in the immersion medium (open squares).
  • the topographic asphericities of the refractive surfaces of the intraocular lens according to the invention in any case assume negative values less than -1, that is to say the surfaces are always hyperbolic. This applies in particular also in the case of an IOL according to the invention which only has a convex surface.
  • the asphericity in an IOL with only one hyperbolic-aspherical surface is always greater than in the case of a symmetrical IOL.
  • the values of the asphericity shown in FIGS. 4 and 5 represent minimum values in this 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 Di> +3 dpt is less than -1.
  • the topography of at least one of the refractive surfaces can always be described by a hyperboloid.
  • FIGS. 4 and 5 it can also be seen from FIGS. 4 and 5 that such an IOL breaks an incident, plane wave into an outgoing wave with a hyperbolic curved wavefront, because the asphericity of the outgoing wave asph 0 u ⁇ is in any case below -1.
  • the hyperbolic wavefront preferably has an asphericity asph 0 u ⁇ ⁇ -5.
  • a conventional IOL with spherically curved surfaces has a positive spherical aberration, i.e. it breaks an incident wave with a flat wavefront into an outgoing wave with an elliptically oblong curved wavefront.
  • Refractive index of the lens material of 1.46 in particular also in the immersion medium.
  • an IOL according to the first embodiment of the present invention can therefore be distinguished from an intraocular lens according to the prior art if it is known when the refractive index is known, when it is illuminated with a plane wave.
  • a corresponding measurement in vitro can be carried out in a standardized measurement setup and need not be carried out in the human eye.
  • An example of such a measurement setup is shown in FIG. 6. It essentially corresponds to a structure 610 known from the ISO 11979-2 standard, consisting of an arrangement of optical elements for generating a plane wave, ie for generating and collimating a parallel beam with which an IOL 614 to be measured is illuminated.
  • the wavefront analyzer breaks down the beam 616 coming from the IOL into a multiplicity of beams 624 by means of a lens arrangement 622, the local distribution of which is detected by means of a light detector 626, such as a CCD camera. Based on the distribution, conclusions about the waveform can be drawn in a known manner by means of an image evaluation device (not shown). With this method, the imaging properties of the IOL to be examined can be determined.
  • the results do not allow any clear conclusions to be drawn about the material properties and the topographic parameters of the intraocular lens, since the same imaging properties can be achieved with intraocular lenses with different refractive indices and surface curvatures.
  • the examination of the IOL depends on its optical properties, so that this method is universally used compared to known methods, the evaluation of which is based on the topology of spherical lenses and which are therefore unsuitable for measuring the IOL according to the invention can.
  • This measurement method is therefore suitable, in particular, to distinguish an IOL according to the invention from a conventional spherical IOL, since, as shown above, these differ precisely due to their characteristic imaging properties. separates.
  • the measurements of the imaging properties of the IOL to be measured can be carried out with this measurement setup, preferably in the ambient medium air but also in the immersion medium.
  • the refractive properties for intraocular lenses with refractive powers in the interval between 3 dpt and 35 dpt are selected.
  • the intraocular lenses according to the invention are not restricted to these refractive powers. Larger refractive powers can also be selected and can be extrapolated in a simple manner due to the continuous course of the curves.
  • the above considerations were exemplary for 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 is not restricted to an IOL with the stated values for the refractive index, the diameter or the edge thickness.
  • the IOL according to a second embodiment of the present invention has a central refractive power in the immersion medium Di of at most -2 dpt.
  • Such an IOL according to the invention also breaks with a corresponding curvature of the lens surface, i.e. with a refractive power decreasing towards the edge of the lens (negative spherical aberration), an incident wave with an elliptically oblong curved wavefront into an outgoing spherical wave.
  • Such a lens according to the invention converts an incident plane wave into an outgoing wave with an elliptically oblong curved wave front.
  • a conventional spherical lens of positive refractive power converts an incident plane wave into a wave with an elliptically oblong curved wavefront, ie the refracted marginal rays experience a greater deflection than the central rays.
  • point spherical lenses with positive refractive power have a positive spherical aberration. Accordingly, aberration is negative for a spherical lens with negative refractive power.
  • Such a lens converts an incident plane wave into an outgoing wave with a wavefront that is also elliptically oblong curved.
  • the wave fronts measured in the immersion medium when examining the IOL according to the invention have a positive asphericity which is 1600- to 20 times greater than that of a conventional spherical IOL, in each case depending on the refractive power of the lenses.
  • the wavefronts generated by the IOL according to the invention face those of a conventional spherical lens.
  • th wave fronts increased positive asphericity by 500 to 8.5 times, again depending on the refractive power of the lenses.
  • the asphericity of a spherical IOL with negative refractive power in air regardless of its amount, does not reach values that are greater than +10.
  • the two emerging waves can therefore be easily distinguished by the degree of their asphericity. If the refractive power of the lenses is known, the device according to FIG. 6 can again be used to distinguish whether the lens under investigation is a conventional spherical IOL or an IOL according to the invention.
  • An intraocular lens according to a third embodiment of the present invention has a central refractive power 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 center.
  • 7 shows a cross section of a symmetrical IOL 700 with a refractive power in the center of +2 dpt.
  • FIGS. 8 and 9 show the course of the wave fronts of outgoing waves which are generated 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 irradiated.
  • the meridian of the wavefront generated by the IOL according to the invention has an inflection point, whereas the wavefront generated by a conventional lens is monotonous runs. This applies both in the ambient medium air, cf. Fig. 8, as well as in immersion medium, cf. Fig. 9.
  • This allows lenses according to the invention with the above-mentioned refractive power to be clearly distinguished from conventional spherically curved lenses, likewise by the method described in connection with FIG. 6.

Landscapes

  • 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)

Abstract

L'invention concerne une lentille intraoculaire à aberration de sphéricité négative et un procédé pour déterminer le pouvoir réfringent de lentilles intraoculaires. Dans l'environnement d'un agent d'immersion, une lentille intraoculaire réfracte une onde incidente à front d'onde à courbe oblongue elliptique en une onde de fuite à front d'onde sensiblement sphérique.
EP04736052A 2003-06-06 2004-06-04 Lentille intraoculaire Withdrawn EP1635740A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10325841A DE10325841A1 (de) 2003-06-06 2003-06-06 Intraokularlinse
PCT/EP2004/006074 WO2004108017A1 (fr) 2003-06-06 2004-06-04 Lentille intraoculaire

Publications (1)

Publication Number Publication Date
EP1635740A1 true EP1635740A1 (fr) 2006-03-22

Family

ID=33482675

Family Applications (1)

Application Number Title Priority Date Filing Date
EP04736052A Withdrawn EP1635740A1 (fr) 2003-06-06 2004-06-04 Lentille intraoculaire

Country Status (7)

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

Families Citing this family (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102005028933A1 (de) * 2005-06-22 2006-12-28 Acri.Tec Gesellschaft für ophthalmologische Produkte mbH Astigmatische Intraokularlinse
US7261412B2 (en) * 2005-06-30 2007-08-28 Visx, Incorporated Presbyopia correction through negative high-order spherical aberration
US7879089B2 (en) * 2006-05-17 2011-02-01 Alcon, Inc. Correction of higher order aberrations in intraocular lenses
WO2009076500A1 (fr) * 2007-12-11 2009-06-18 Bausch & Lomb Incorporated Procédé et appareil pour fournir des systèmes optiques oculaires présentant des profondeurs de champ étendues
US8331048B1 (en) 2009-12-18 2012-12-11 Bausch & Lomb Incorporated Methods of designing lenses having selected depths of field
US10052195B2 (en) 2010-11-15 2018-08-21 Elenza, Inc. Adaptive intraocular lens
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
CN108714063B (zh) 2012-10-17 2021-01-15 华柏恩视觉研究中心 用于屈光不正的镜片、装置、方法和系统
CN111265331B (zh) 2014-09-09 2022-09-09 斯塔尔外科有限公司 具有扩展的景深和增强的远距视力的眼科植入物
KR102457572B1 (ko) 2016-03-09 2022-10-20 스타 서지컬 컴퍼니 확장된 피사계 심도 및 향상된 원거리 시력의 안과용 임플란트
WO2019067033A2 (fr) * 2017-06-15 2019-04-04 Analog Photonics LLC Structures optiques intégrées pour lidar et autres applications employant de multiples détecteurs
EP4235275A3 (fr) 2018-08-17 2023-12-13 Staar Surgical Company Composition polymère présentant un nanogradient d'indice de réfraction

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US20020105617A1 (en) * 2000-05-23 2002-08-08 Sverker Norrby Methods of obtaining ophthalmic lenses providing the eye with reduced aberrations

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US4504982A (en) * 1982-08-05 1985-03-19 Optical Radiation Corporation Aspheric intraocular lens
JP2859001B2 (ja) 1991-07-11 1999-02-17 株式会社メニコン 非球面眼用レンズおよびその製造方法
EP1248093A1 (fr) * 1994-06-14 2002-10-09 Visionix Ltd. Dispositif de mappage des systèmes optiques
IL118065A0 (en) * 1995-05-04 1996-08-04 Johnson & Johnson Vision Prod Aspheric toric lens designs
DE10006896A1 (de) * 2000-02-16 2001-08-30 Wavelight Laser Technologie Ag Verfahren zum Herstellen einer künstlichen okularen Linse
US7048759B2 (en) * 2000-02-24 2006-05-23 Advanced Medical Optics, Inc. Intraocular lenses
WO2001089424A1 (fr) * 2000-05-23 2001-11-29 Pharmacia Groningen Bv Procedes de production de lentilles ophtalmiques capables de reduire des aberrations de l'oeil
US6533416B1 (en) * 2001-07-20 2003-03-18 Ocular Sciences, Inc. Contact or intraocular lens and method for its preparation

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Publication number Priority date Publication date Assignee Title
US20020105617A1 (en) * 2000-05-23 2002-08-08 Sverker Norrby Methods of obtaining ophthalmic lenses providing the eye with reduced aberrations

Non-Patent Citations (1)

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Title
See also references of WO2004108017A1 *

Also Published As

Publication number Publication date
US20090270983A1 (en) 2009-10-29
JP2006527014A (ja) 2006-11-30
KR20060037263A (ko) 2006-05-03
CA2528024A1 (fr) 2004-12-16
KR100866442B1 (ko) 2008-10-31
KR20070097132A (ko) 2007-10-02
CA2528024C (fr) 2012-07-31
US20060167545A1 (en) 2006-07-27
WO2004108017A1 (fr) 2004-12-16
DE10325841A1 (de) 2004-12-30
US8066767B2 (en) 2011-11-29

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