EP1845836A1 - Utilisation d'un aberrometre a analyse du front d'onde - Google Patents

Utilisation d'un aberrometre a analyse du front d'onde

Info

Publication number
EP1845836A1
EP1845836A1 EP05731055A EP05731055A EP1845836A1 EP 1845836 A1 EP1845836 A1 EP 1845836A1 EP 05731055 A EP05731055 A EP 05731055A EP 05731055 A EP05731055 A EP 05731055A EP 1845836 A1 EP1845836 A1 EP 1845836A1
Authority
EP
European Patent Office
Prior art keywords
lens
symmetry
eye
artificial
major axis
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Withdrawn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
EP05731055A
Other languages
German (de)
English (en)
Other versions
EP1845836A4 (fr
Inventor
L. Waltz Kevin, M.D.
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.)
Individual
Original Assignee
Individual
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 Individual filed Critical Individual
Publication of EP1845836A1 publication Critical patent/EP1845836A1/fr
Publication of EP1845836A4 publication Critical patent/EP1845836A4/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Withdrawn legal-status Critical Current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
    • 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
    • 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
    • A61F2/1624—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 having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside

Definitions

  • This invention relates to optics, and, more particularly, to a method for using a wavefront aberrometer to assist in determining the proper orientation of a surgically implantable artificial lens or other surgical treatment for presbyopia.
  • the human eye is one of the imperfectionss of evolution. As illustrated in FIG. 1 , light 1 enters the eye 2 through the cornea 3 and pupil 4.
  • the pupil 4 is an aperture of variable size formed through the iris 5.
  • Light travels through the pupil 4 through the lens 6 (sometimes referred to as the crystalline lens 6), where it is redirected and is focused on the back wall or retina 7.
  • the pattern of light falling on the retina 7 forms an image that is detected by detectors distributed over the retina 7.
  • the detectors transducer the light energy impinging upon them to nerve impulses that are transmitted to the brain via the optic nerve 8, where the impulses are interpreted as sight.
  • the eye 2 is generally spherical in shape and has an average diameter of generally about 24 milimeters.
  • the eye ball 2 is defined by the cornea 3 and sclera 9 (an outer cover membrane), the choroid 10 (an interior region containing the network of blood vessels servicing the eye 2) and the retina 7.
  • the cornea 3 is tough transparent tissue that covers the front portion of the eye 2.
  • the sclera 9 is an opaque membrane that connects to the cornea 3 and encloses the remainder of the eye 2.
  • the choroid 10 includes a ciliary body 1 1 and the an iris diaphragm 5.
  • the pupil 4 of the iris diaphragm 5 contracts and expands to control the size of the pupil 4 and thus the amount of light 1 that may enter the eye 2.
  • the lens 6 is made up of concentric layers of transparent fibrous cells and is suspended by fibers or zonules 12 that attach to the ciliary body 1 1. As illustrated in FIGs. 2A and 2B, the lens 6 operates to focus light 1 travelling therethrough by changing its shape. More specifically, when the ciliary muscle 1 1 connected to the fibers 12 relaxes, the changes in the ciliary processes 1 1 cause changes in the curvature of the lens 6 (such as flattening or becoming less convex and thus enabling the lens 6 to focus light 1 from objects at a remote distance [see FIG. 2A] or contracting or becoming more convex to enable the eye 2 to refocus on an object at a closer distance [see FIG. 2B]).
  • accommodation This adjustment in the shape of the lens 6 to focus at various distances is referred to as “accommodation” or the “accommodative process” and is associated with a concurrent change in dimension of the pupil 4. Accommodation is also associated with changes in corneal curvature, constriction of the pupil, an increase in higher order aberrations, and convergence or medial rotations of the two eyes 2.
  • the innermost membrane of the eye is the retina 7, which lies on the inside of the entire back wall portion of the eye 2.
  • the main receptors are rod cells (or rods) that take part in black and white imaging and cone cells (or cones) that take part in color vision.
  • the cones tend to be centralized in the middle portion of the retina 7, called the fovea 13 (or macula).
  • the cones are highly sensitive to color and thus allow the brain to experience color vision.
  • the rods are more evenly distributed over a much larger area and provide the brain with a more general image of the field of view.
  • an aberration is any perceived or real imperfection in the formation of a visual image.
  • Aberrations may be regular and measurable, such as spherical aberration, chromatic aberration, and coma. Alternately, aberrations may be irregular, as might be noticed when looking through a pane of handblown glass. Instruments that measure aberrations of the visual system are called 'wavefront analyzers' or aberrometers.
  • Coma is a lens aberration that results from different magnifications happening in different portions of the lens.
  • Light rays 1 traveling through the center of a lens 6 can be focused to a point. If light rays 1 go through the lens 6 off-axis (at an angle), the light rays 1 will not focus to a point and the image thus appears as a fuzzy circle. The farther off-axis the path of the light rays 1, the larger the fuzzy circle, yielding imaged objects having comet-like appearances (hence the term "coma").
  • Coma is typically observed in the outer portions of an image field that is some distance from the principal axis of the eye 2.
  • Astigmatism is a vision defect arising from the radius of curvature of the optics of the eye 2, especially the cornea 3, being unequal at different orientations around the visual axis. Lines or bars at different orientations are not all simultaneously in focus, and thus there may be distortions for some orientations.
  • Myopia or near-sightedness, is a defocus aberration wherein vision is better close-up than at a distance, and is corrected by concave lenses.
  • Hyperopia or far-sightedness, is the opposite condition wherein objects at a distance more easily resolved than closer objects. Hyperopia is corrected by convex lenses.
  • Presbyopia is a condition characterized by a loss of flexibility in the natural lens 6. When young, the natural lens 6 is quite flexible and easily accommodates for close focus. As it ages, the lens 6 accumulates layers of protein acumulate on its outer surface (akin to the growth rings in a tree trunk). The lens 6 thus becomes thicker, denser, and less flexible and, as a result, close focusing becomes difficult.
  • Optical aberrations such as myopia, hyperopia and astigmatism, as well has many other higher order aberrations, blur images formed on the retina and thus impair vision.
  • Higher order aberrations include subtle, regular and measureable imperfections in the lens that are not corrected with simple sphero-cylindrical lenses.
  • An astronomer and mathematician in the early 20th Century named Fritz Zernike developed a series of polynomial equations to describe low-order and higher-order aberrations in lathe-cut lenses. These equations, dubbed Zernike polynomials, form the basis for analysis and decription of aberration patterns in many current systems designed for wavefront analysis of the human eye 2.
  • Cataracts occur when the eye's lens 6 becomes cloudy or opaque. Eventually, the lens 6 will become so opacified that vision becomes significantly impaired. When this occurs, the natural lens 6 may be removed via cataract surgery. Typically, the natural lens 6 is replaced via intraocular lens implantation (IOL) surgery, wherein an artificial lens 20 is implanted in the eye 2. (See FIG. 3). Generally, artificial lenses 20 have been assumed to be stationary and hard, and thus unable to adjust to focus or accommodate.
  • IOL intraocular lens implantation
  • new accommodating artificial lenses 30 have been developed that allow the eye 2 to focus, and thus enable a patient having an implanted lens 30 to enjoy both near and far focus.
  • These lens systems 30 are elongated in design, with a pair of connectors or haptics 32 oriented linearly (i.e., with one-hundred and eighty degree separation) about an artificial optical lens member 34.
  • the artificial lens system 30 further includes at least one hinge or flexure point 36 formed in a haptic 32 to accommodate such changes in focus. As shown in FIGs.
  • the hinge(es) 36 are connected between the some of the zonules 12 and the lens member 34, and thus enable the lens member 34 to move within the eye 2 in response to changes in tension of the zonules 12 to thus change the focus of the eye 2.
  • One drawback of the artificial accommodating lens 30 arises from its partial asymmetry.
  • the lens system 30 is characterized by 180-degree rotational symmetry about an axis of rotation passing through the lens member 34 and oriented perpendicular to an axis or line 38 passing through the lens member 34 and the haptics 32. This line 38 may be thought of as a major axis of symmetry of the lens system 30.
  • the lens 30 functions to allow accommodation is at least partially a function of its orientation relative in the eye 2. More particularly, the ability of the lens system 30 to allow focus is at least partially a function of the strength, resilience and integrity of the zonules 12 to which it is attached and the ciliary muscles to which the zonules 12 are attached. If those zonules 12 and muscles are weak and loose, they may not be able to actuate flexure/movement of the artificial lens system 30 to change the focus of the eye 2. Further, the lens system 30 may experience some degree of lateral movement and/or change in surface curvature of the IOL in the eye 2.
  • the degree of controlled (or uncontrolled) effective changes in the curvature of the lens system 30 and/or lateral movement of the lens system 30 may be a function of the strength and/or resilience of the muscles 1 1 and zonules 12 to which the lens system 30 connects.
  • the present invention relates to method and apparatus for determining the proper orientation for implantation of an accommodating lens system in the eye.
  • One object of the present invention is to provide an improved method of orienting a lens system for surgical implantation in an eye.
  • FIG. 1 is a schematic sectional view of the human eye.
  • FIG. 2A is an enlarged sectional view of the human eye with the lens capsule stretched.
  • FIG. 2B is an enlarged sectional view of the human eye with the lens capsule relaxed.
  • FIG. 3 is an enlarged plan view of an artificial implantable lens known in the prior art.
  • FIG. 4 is an enlarged plan view of an artificial implantable accommodating lens known in the prior art and having hinged haptics.
  • FIG. 5A is a schematic diagram of the prior art lens system of FIG. 4 with the haptics oriented at a first angle relative the lens to provide a relatively long haptic arm length.
  • FIG. 5B is a schematic diagram of the prior art lens system of FIG. 4 with the haptics oriented at a second angle relative the lens to provide a relatively short haptic arm length.
  • FIG. 6A is an enlarged sectional perspective view of the prior art lens of FIG. 4 as implanted in an eye and occupying a first, relaxed position.
  • FIG. 6B is an enlarged sectional perspective view of the prior art lens of FIG. 4 as implanted in an eye and occupying a second, vaulted position.
  • FIG. 7A is a sectional side elevation view of the prior art lens of FIG. 4 as implanted in an eye and occupying an unflexed orientation to accommodate intermediate vision.
  • FIG. 7B is a sectional side elevation view of the prior art lens of FIG. 4 as implanted in an eye and occupying an anteriorially flexed orientation to accommodate intermediate near vision.
  • FIG. 7C is a sectional side elevation view of the prior art lens of FIG. 4 as implanted in an eye and occupying a posteriorally flexed orientation to accommodate distance vision.
  • FIG. 8 A is a graphical representation of the wavefront comparison display showing the orientation of lens aberrations for a first eye of a relatively young patient not requiring corrective lenses.
  • FIG. 8B is a graphical representation of the wavefront comparison display showing the orientation of lens aberrations for a second eye of the relatively young patient not requiring corrective lenses.
  • FIG. 9A is a graphical representation of the wavefront comparison display showing the orientation of lens aberrations for a first eye of a relatively old patient requiring corrective lenses of moderate strength.
  • FIG. 9B is a graphical representation of the wavefront comparison display showing the orientation of lens aberrations for a second eye of the relatively old patient requiring corrective lenses of moderate strength.
  • FIGs. 8A-9B relate to a first embodiment of the present invention, a method for determining the orientation of an artificial accommodating lens 30 necessary to substantially optimize the ability of the patient to focus on both near and far objects after surgery.
  • the recipient of an artificial accommodating lens 30 is expected to have more ability to change the focus of the post-surgery eye 2 because the lens 30 has the ability to move within the eye, thus enabling a change of focus.
  • the lens 30 may move by vaulting toward the front or the back of the eye 2 (anterior and posterior vaulting), by laterally moving from side to side along its axis 38 as it is pulled to and fro by the cilial muscles 1 1 and zonules 12 to which it is connected, by modifying the anterior or posterior curvature of the crystalline lens or artificial lens or by any combination of the mechanisms. Vaulting movement moves the entire lens forward or backward to change focal length, while lateral movement changes the lens thickness through which the light 1 travels.
  • Anterior or posterior lens curvature changes may be symmetrical or asymmetrical about the visual axis. Either mechanism (or all) operate to change the focus of the eye 2, and all mechanisms are initiated by contractions and expansions of the cilial muscles 1 1 and zonules 12.
  • a wave front aberrometer may be used to map the pattern of aberrations 38 in the eye 2 while the eye 2 is focused on a target or targets positioned at different distances.
  • the contribution of surface aberrations may be subtracted to isolate the aberration contributions from the lens 6, which are graphed as a calculated differential aberration pattern 40.
  • These differential aberattion patterns 40 may be plotted to reveal the orientations, if any, of the aberration of the lens 6. Referring to FIGs. 8A and 8B, differential aberration plots 40 were generated for the eyes of a relatively young, optically healthy patient not in need of any corrective lenses. The differential plots reveal only minor lens aberrations uncharacterized by any major axes of orientation or directional components.
  • FIGs. 9A and 9B differential aberration plots 40 taken of the eyes of an older patient requiring corrective lenses of moderate strength for myopia, reveal lens aberrations with significant directionality as illustrated by axes of symmetry 42.
  • Aberration axes 42 may be generated from the differential aberration plots 40, and such axes 42 may be used to determine the best orientation for the placement of an artificial accommodating lens 30.
  • the aberration axes 42 are indicative of the direction across the lens 6 wherein the eye 2 is able to generate the greatest force to achieve the largest amount of accommodation.
  • This directionality is a result of nonuniform lens thickening and/or stiffening, local weakening of the zonules 12 and/or the cilial muscles 1 1 at certain positions around the iris, or a combination of the two.
  • the examples of FIGs. 9A and 9B include two relatively orthogonal axes 42, the axes 42 do not necessarily have to be orthogonal to one another and may lie at other angular relationships. Likewise, there may be other numbers of axes 42 besides two, such as a single axis of symmetry 42 or three or more distinct axes 42.
  • a wavefront aberrometer is used to determining the optimum orientation for the implantation of an artificial accommodating lens 30 by first generating a first aberration map 38 of an eye 2 as focused on an object located substantially at infinity and generating a second aberration map 38 for the same eye 2 as focused on an object located relatively nearby.
  • the first and second maps 38 are compared to mathematically subtract the aberration contributions from the surface of the eye to yield an aberration map 40 of the lens 6.
  • the aberration map 40 of the lens 6 is analyzed to determine if any axes of symmetry of aberrations of the lens 6 exist and, if so, to identify the major axis of symmetry 42 of the aberrations of the lens 6; such an axis 42 is indicative of the orientation of the major aberrations of the lens 6 and is typically the most pronounced axis 42 visible.
  • the axis of symmetry of the artificial lens 30 is then identified and the axis of the lens 30 is aligning relative the aberration axis of symmetry 42 to provide optimal lens 30 function.
  • the lens 30 is then implanted into the eye 2 at this orientation.
  • the artificial accommodating lens 30, as discussed above, generally includes a circular lens disc and at least one generally linear elongated haptic member extending therefrom; more typically, the artificial accommodating lens 30 includes a generally circular lens disc and a pair of oppositely disposed generally linear elongated haptic members extending therefrom to define its axis.
  • an optimized orientation for an implantable artificial lens 30 is determined by conducting wavefront aberration analysis of an eye 2 to generate a refraction map 38 of the aberrations of the eye 2, isolating the aberration contributions from the lens 6 of the eye 2, and determining if a major axis of symmetry 42 of the aberration of the lens 6 of the eye 2 is present. If a major axis of symmetry 42 of the aberration of the lens 6 of the eye 2 is present, the haptics of the artificial accommodating lens 30 are oriented relative the major axis of symmetry 42. If a major axis of symmetry 42 of the aberration of the lens 6 of the eye 2 is not present, the haptics of the artificial accommodating lens 30 are oriented at will. The so oriented artificial accommodating lens 30 is then implanted into the eye 2.
  • the same techniques may be used for patients already having an implanted artificial lens system 30.
  • the near vision of a patient having an implanted artificial lens system 30 may be measured and evaluated to determine if the lens system 30 is not functioning correctly (i.e., if the lens system 30 is not focusing as it should) and a modified surgical plan may then be developed to address and correct the situation.
  • the above techniques may be used to estimate the lost accommodation patterns for an adult based on those of a genetic relative, such as a child, who still retains some or all of his original accommodation.
  • This technique for estimating the original and now lost or partially lost (or extinguished) accommodation pattern for the older patient is based on the assumption that close genetic relatives have a high likelihood of having similar accommodation patterns; thus, measurement of the accommodation patterns of one or more close genetic relatives may yield pattern information that will allow the generation of an estimated accommodation pattern for the older patient that approximates the original accommodation pattern enjoyed in youth and thus allow the physician to select the best lens type (accommodative, pseudoaccommodative [monofocal or multifocal]) to best restore some or all of the patient's original accommodative pattern.
  • This process could also be used to determine the orientation of the specific IOL used to restore the accommodation.
  • the brain response plays an important role in interpreting the accommodative pattern of the eye.
  • the above technique may be used in conjunction with brain analysis techniques, such as PET scans, MRI scans, ECG's and the like, to indicate first if the patient is capable of making an accommodative lens function properly and, if so, which type of accommodative lens is likely to work best for that patient.

Landscapes

  • Health & Medical Sciences (AREA)
  • Ophthalmology & Optometry (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (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

Technique d'utilisation d'un aberromètre à analyse du front d'onde pour orienter une lentille artificielle à axe principal de symétrie pour implantation dans l'oeil. Cette technique consiste à activer ledit aberromètre et à générer une carte des schémas d'aberration de l'oeil, puis à identifier un axe principal de symétrie de ces schémas d'aberration. Semblablement, on identifie l'axe de symétrie principal de la lentille artificiel et l'on aligne les deux axes principaux de symétrie. On implante ensuite la lentille dans l'oeil stout en maintenant les axes de symétrie alignés.
EP05731055A 2005-02-10 2005-03-30 Utilisation d'un aberrometre a analyse du front d'onde Withdrawn EP1845836A4 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US5470005A 2005-02-10 2005-02-10
PCT/US2005/010672 WO2006085889A1 (fr) 2005-02-10 2005-03-30 Utilisation d'un aberrometre a analyse du front d'onde

Publications (2)

Publication Number Publication Date
EP1845836A1 true EP1845836A1 (fr) 2007-10-24
EP1845836A4 EP1845836A4 (fr) 2009-04-29

Family

ID=36793347

Family Applications (1)

Application Number Title Priority Date Filing Date
EP05731055A Withdrawn EP1845836A4 (fr) 2005-02-10 2005-03-30 Utilisation d'un aberrometre a analyse du front d'onde

Country Status (2)

Country Link
EP (1) EP1845836A4 (fr)
WO (1) WO2006085889A1 (fr)

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2012129508A1 (fr) * 2011-03-24 2012-09-27 Innovative Visual Systems Llc Retro-éclairage et alignement de caractéristiques de surface antérieure de l'œil pour une topographie cornéenne et un système de front d'ondes oculaire

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2002051338A1 (fr) * 2000-12-22 2002-07-04 Pharmacia Groningen Bv Procedes permettant d'obtenir des lentilles ophtalmiques donnant a l'oeil des aberrations reduites
WO2003032825A1 (fr) * 2001-10-19 2003-04-24 Bausch & Lomb Incorporated Attenuation de la presbytie
WO2004090611A2 (fr) * 2003-03-31 2004-10-21 Bausch & Lomb Incorporated Lentilles intraoculaires et procede pour diminuer les aberrations dans un systeme oculaire
WO2004107020A2 (fr) * 2003-05-24 2004-12-09 Valdemar Portney Lentille intra-oculaire a profil etroit

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6197059B1 (en) * 1990-04-27 2001-03-06 Medevec Licensing, B.V. Accomodating intraocular lens
SG154324A1 (en) * 2001-04-18 2009-08-28 Bausch & Lomb Objective manifest refraction

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2002051338A1 (fr) * 2000-12-22 2002-07-04 Pharmacia Groningen Bv Procedes permettant d'obtenir des lentilles ophtalmiques donnant a l'oeil des aberrations reduites
WO2003032825A1 (fr) * 2001-10-19 2003-04-24 Bausch & Lomb Incorporated Attenuation de la presbytie
WO2004090611A2 (fr) * 2003-03-31 2004-10-21 Bausch & Lomb Incorporated Lentilles intraoculaires et procede pour diminuer les aberrations dans un systeme oculaire
WO2004107020A2 (fr) * 2003-05-24 2004-12-09 Valdemar Portney Lentille intra-oculaire a profil etroit

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of WO2006085889A1 *

Also Published As

Publication number Publication date
WO2006085889A1 (fr) 2006-08-17
EP1845836A4 (fr) 2009-04-29

Similar Documents

Publication Publication Date Title
US11061255B2 (en) Ophthalmic lens comprising lenslets for preventing and/or slowing myopia progression
JP3341058B2 (ja) 角膜の湾曲を変えるための方法
US6623522B2 (en) Myopic corneal ring with central accommodating portion
US5806530A (en) Method for altering the pupil of an eye
US5800532A (en) Asymmetric intraocular lens
JP3448307B2 (ja) 眼内移植片
US20030097177A1 (en) Posterior chamber phakic lens
CN112587282A (zh) 眼内透镜系统
EP2823789A1 (fr) Implant intraoculaire à petite ouverture (trou d'épingle) pour augmenter la profondeur d'un foyer
WO1990012552A1 (fr) Lentille intraoculaire rectifiee
US20230044370A1 (en) Intraocular lens and methods for optimization of depth of focus and the image quality in the periphery of the visual field
US12036111B2 (en) Method of implantation of an intraocular lens in a ciliary sulcus of an eye
ES2877762B2 (es) Método para diseñar y fabricar una lente intraocular
WO2006085889A1 (fr) Utilisation d'un aberrometre a analyse du front d'onde
CA2333734C (fr) Lentille artificielle comprenant un systeme de lentilles multifocal ayant un axe excentre et procede s'y rapportant
US11638642B2 (en) Ophthalmic device having opaque and decentered light-transmissive portions for alleviating symptoms relating to ocular diseases
US20090030513A1 (en) Multifocal Phakic Intraocular Lens
RU2792078C2 (ru) Офтальмологические линзы, содержащие элементарные линзы, для предотвращения и/или замедления прогрессирования миопии
AU2002340418A1 (en) Myopic corneal ring with central accommodating portion

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

17P Request for examination filed

Effective date: 20070816

AK Designated contracting states

Kind code of ref document: A1

Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HU IE IS IT LI LT LU MC NL PL PT RO SE SI SK TR

DAX Request for extension of the european patent (deleted)
A4 Supplementary search report drawn up and despatched

Effective date: 20090330

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: THE APPLICATION HAS BEEN WITHDRAWN

18W Application withdrawn

Effective date: 20090618