WO1987007496A1 - Construction de lentille intra-oculaire bifocale en une seule piece - Google Patents

Construction de lentille intra-oculaire bifocale en une seule piece Download PDF

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Publication number
WO1987007496A1
WO1987007496A1 PCT/US1987/001284 US8701284W WO8707496A1 WO 1987007496 A1 WO1987007496 A1 WO 1987007496A1 US 8701284 W US8701284 W US 8701284W WO 8707496 A1 WO8707496 A1 WO 8707496A1
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WO
WIPO (PCT)
Prior art keywords
lens
lens portion
intraocular
focal length
intraocular lens
Prior art date
Application number
PCT/US1987/001284
Other languages
English (en)
Inventor
Richard H. Keates
Richard P. Schneider
Original Assignee
Precision-Cosmet Co., Inc.
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 Precision-Cosmet Co., Inc. filed Critical Precision-Cosmet Co., Inc.
Publication of WO1987007496A1 publication Critical patent/WO1987007496A1/fr

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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
    • A61F2/1616—Pseudo-accommodative, e.g. multifocal or enabling monovision
    • A61F2/1618—Multifocal lenses

Definitions

  • This invention relates generally to intraocular lenses to be used as artificial lens implants in eyes from which the cataractous natural lens has been removed, and more particularly to an improved rigid lens having multiple lenses.
  • an intraocular lens for restoring vision after cataract surgery is well-known in the art.
  • two forms of surgery are used to remove cataracts. These are extracapsular cataract extraction and intracapsular extraction.
  • an intraocular lens is normally implanted in either the anterior or the posterior chamber of the eye.
  • the lens is generally situated forward of, or mounted to, the iris.
  • the lens is situated behind the iris and may be mounted within the cleft or fornix of the capsule which remains in place after extracapsular surgery.
  • the lens In both anterior or posterior chamber implants, the lens is usually centered and fixed in position by one or more supporting strands or haptic members.
  • the typical haptic member is a flexible strand of non-biodegradable material which is fixed to the lens body, and exhibits specific spring-like memory qualities so that the haptic member can be compressed or off-set from the normal rest position and thereafter returned to the fully extended condition when pressure is removed.
  • the intraocular implant is an artificial lens which has one given focal length. Since the intraocu ⁇ lar implant is made of a rigid material it cannot change the focal length by deformation as the natural lens does (called accommodation). As a result of this, if the focal length is selected to provide a sharp image for a distant object, then an object which is closer (i.e. at reading distance) will not be imaged sharply on the retina. Alternately, one could image closer objects sharp by selecting a different focal length, but then, of course, distant objects would appear out of focus.
  • the present invention addresses the problems associated with the prior art intraocular lenses in that they have not provided for a rigid multi-focal length lens.
  • the present invention provides for such a multi-focal length intraocular lens.
  • the present invention is a rigid bifocal intraocular lens adapted for uses in artificial lens implant.
  • a single rigid implant is provided having one or more additional lenses ground into it, so as to function like bifocal glasses.
  • a plurality of lens por ⁇ tions are formed in the intraocular lens and each lens portion is substantially non-movable with respect to the other(s) .
  • the intraocular lens of the first embodiment has an optical lens body with a central, circular, lens portion and an outer, annular, lens portion.
  • the central, or first, lens portion has a focal length and the second, or outer, annular lens portion has a focal length different from the focal length of the first lens portion.
  • the relative areas of the two lens por- tions may vary, and in the first embodiment described the two are about the same size. However, preferably the diameter of the outer annulus is about 6-7 millime ⁇ ters, whereas the overall diameter of the inner cir ⁇ cular lens portion is between about 1.8 and about 2.2 millimeters.
  • the relative corrective powers of the lens portions may also vary; however, preferably, the corrective factor of the outer (annular) lens portion is between about +5 and +25 diopters, whereas the corrective power of the inner portion is between about +2 and +4 diopters larger than the power of the annular portion. That is, the inner portion preferably has a corrective or add factor of between about +2 and +4 diopters with respect to the outer portion.
  • the first and second lens portions form an integral, one-piece, bifocal optical lens body.
  • the intraocular lens of an alternate embodiment has an optical lens body having a chord and first and second lens portions.
  • the first lens portion has a focal length and the second lens portion has a focal length different from the focal length of the first lens portion.
  • the first lens portion is positioned on one side of the chord and the second lens portion is positioned on the other side of the chord.
  • the first and second lens portions form an integral, one-piece bifocal optical lens body wherein the first and second lens portions are substantially non-movable with respect to one another.
  • the lens body is substantially circular and the chord is a diameter of the lens body.
  • the images from both lens portions for either embodiment should end up in the same plane. That is, the powers of the two lens por ⁇ tions should be selected so that the image from infi ⁇ nity projected through the second lens portion will be focused in about the same plane as the image from a close object being located at standard reading distance projected through the first lens portion.
  • both of the first and second lens portions may produce images substantially superimposed on one another. Depending on the distance to the object(s) being viewed and the amount of light present, one of the images will appear sharp and the other sufficiently defocused to permit the user's brain to select the sharper image for evaluation.
  • Figure 1 is a cross-sectional view of the eye and shows a lens incorporating our present invention implanted in the posterior chamber of the eye.
  • Figure 2 is a top plan view of the lens of Figure 1, shown according to a first embodiment of the invention.
  • Figure 2A is generally the same as Figure 2, except Figure 2A is reduced, is fragmentary, and shows different relative sizes between various lens portions.
  • Figure 3 is a side elevational view of the lens shown in Figure 1.
  • Figure 4 is a top plan view of a second embodi ⁇ ment of the present invention.
  • Figure 5 is a side elevational view of the lens shown in Figure 4.
  • Figure 6 is a cross-sectional view, taken along the line 6-6 of Figure 4.
  • Figure 7 is a cross-sectional view of the eye and shows a lens incorporating an embodiment of our present invention implanted in the posterior chamber of the eye; the lens being a plano-convex variation of the embodiment shown in Figure 1.
  • Figure 8 is a top plan view of the lens of Figure 7.
  • Figure 8A is generally the same as Figure 8, except Figure 8A is reduced, is fragmentary, and shows different relative sizes between the various lens por ⁇ tions.
  • an intraocular lens designated generally as 10
  • the intraocular lens 10 includes a rigid optical region or lens body 11 which includes a first lens portion or lens 12 cooperatively connected to a second lens portion or lens 13 to form a lens body or optical region 13.
  • the first lens 12 is an inner lens having an axis 12a.
  • the second lens 13 is an annular lens having an axis 13a.
  • the lens body 11, or optic portion of the intraocular lens 10 is cen ⁇ tered and retained within the eye by retaining means such as haptic members 14 and 15 having first ends 14a and 15a and second ends 14b and 15b respectively.
  • the first ends 14a and 15a are cooperatively connected to the lens body 11 by methods well known in the art.
  • the construction and specific configuration of the haptic members 14 and 15 may be any suitable construction, such construction being well known in the art.
  • the haptic members 14 and 15, inner lens 12 and annular lens 13 are formed as an integral one-piece structure by a forging and machining process.
  • the intraocular lens 10 may also be produced by other suitable methods such as injection molding and lathing.
  • the inner lens 12 and annular lens 13 are substantially non-movable with respect to one another.
  • the unitary intraocular lens body 11, including the first lens 12 and second lens 13, is made of a biological tolerable and optically suitable material such as polymethylmethacrylate (PMMA).
  • PMMA polymethylmethacrylate
  • the haptic mem ⁇ bers 14 and 15 may be .made of a flexible, compressible, resilient plastic material such as PMMA or polypropy ⁇ lene, or other materials as well known in the art.
  • the entire intraocular lens 10 is of an integral one-piece structure and is made of PMMA.
  • the posterior chamber type intraocular lens 10 will typically be utilized following extra capsular cataract extraction.
  • the lens 10 is implanted in a human eye 40, in the posterior chamber 42 behind the iris 44.
  • the cataract has been extracted from the capsular bag 46, leaving intact the posterior wall 46a and an annular flap por ⁇ tion 46b forming a cleft of fornix 46c.
  • the capsular bag 46 is connected to the ciliary muscle in the eye wall 48 via suspensory ligaments 50. Vitreous humor in the region 52 behind the capsular bag 46 is prevented from flowing forward by the posterior wall 46a.
  • the intraocular lens 10 may serve as a bifocal vision system, with one lens 12 for reading and the other lens 13 for distant viewing.
  • the axis 12a of the inner lens 12 is coaxial with the axis 13a of the annular lens 13.
  • the certain principles of the present invention will also be applicable where the axes 12a and 13a are not coaxial.
  • the first lens portion has a focal length that is for viewing near objects and the second lens portion has a focal length that is for viewing distant objects.
  • Such a combination of lenses will produce two images on the retina which are superim ⁇ posed. Always, one of the two images will appear blurred. If an object up close is viewed, the image produced through the second lens will appear blurred; or, if the object is viewed at a distance, the image through the first lens will appear blurred. The user's brain can select the sharper image for evaluation.
  • the first lens 12 is a center lens having a focal length for reading and the second lens 13 is an annular ring shaped lens having a focal length for distant viewing.
  • the area of each lens 12 and 13 will ideally be computed individually for each patient, depending upon the patient's iris reflexes, as described more fully hereafter. In actual practice, a whole series of lenses would probably be provided, having dif- ferent corrective properties, so that an appropriate lens could be selected for any given patient.
  • the area of the first lens 12 would be from approximately 30% to 50% of the area of the lens body 11. Further, it was indicated as preferred that the first lens 12 be approximately 40% of the total area of the lens body 11 or, otherwise stated, the area of the first lens 12 be approximately equal to the area of the second lens 13. This is shown in Fig. 2.
  • Fig. 2A shows an arrange ⁇ ment which is substantially identical to Fig. 2 in substance, but for the relative sizes of the lens por ⁇ tions 12' and 13', to indicate the alternate and pre- ferred possibility.
  • the annular portion have a diameter of about 6.0 to about 7.0 millimeters while the inner portion has a diameter of about 1.8 to about 2.2 millimeters.
  • the area of the first lens portion is between about 6% and 14% of the combined areas of the first and second lens portions.
  • reterence numberals 10', 11' , 12' , 13' , 14', 14a', 15' and 15a' indicate parts generally analogous, in form and function, to parts 10, 11, 12, 13, 14, 14a, 15, and 15a respectively.
  • the desired relative powers between the two lens portions may vary from patient to patient. Generally, for most uses an operable embodiment will have a corrective power of about +15 to about +25 diopters, for the outer lens portion, the portion used for distance viewing; and, a corrective power of about +2 to about +4 diopters larger than the outer lens portion for the inner por ⁇ tion, i.e. that portion used for near viewing.
  • the iris 44 will be open and the image created by the annular lens 13 (which is sharp) will overpower the blurred and also less bright image created by the inner lens 12.
  • the overpowering process is made possible by the fact that blurred edges are less intense than sharp edges, and by the way the image eval ⁇ uation system of the brain works. Reading takes place usually indoors and bright illumination can readily be applied.
  • the iris 44 will close, and the area of the annular lens 13 will be reduced so that the image of the inner lens 12 (which is now sharp) will overpower the blurred, less bright, image generated by the annular lens 13.
  • the brain will accordingly see the sharp image.
  • the image evaluation system of the brain searches for sharp edges and, once it finds a sharp edge, it exaggerates the edge. Therefore, generally, as long as the blurred image is weaker in intensity that the sharp one, the brain will evaluate the images and "see" the sharp image.
  • any suitable combination such as plano-convex, biconcave, meniscus or other com- bination of lenses may be used with either an add on center or a distance on center to provide for the inner lens 12. It is only necessary for one skilled in the art to make a suitable combination of such lenses to provide for a focal length for one of the lenses 12 or 13 for distance reading and a focal length for the other of the lenses 12 or 13 having a focal length for viewing near objects, preferably with both of the len ⁇ ses having a positive power.
  • FIG. 4-6 Another embodiment of the present invention is shown in Figures 4-6.
  • This lens would also be posi ⁇ tioned in the eye as shown in Figure 1.
  • the second embodiment of the implantable intraocular lens 60 inclu ⁇ des a rigid bifocal optical region or lens body 61 which includes a first lens portion 62 and a second lens por- tion 63, the bases of which are coplanar.
  • the lens body 61 has a chord 61a between lens portions 62 and 63.
  • This embodiment is also adapted to be implanted in the posterior chamber, although the concept can be utilized in an anterior chamber lens as well.
  • the unitary optical lens body 61 is substantially circular, the chord 61a is a diameter of the lens body 61 and the lens portions are semicir ⁇ cular.
  • the first and second lens portions may preferably be of about the same size and the lens portions are substantially non-movable with respect to one another.
  • the powers for the near vision and distance vision sections may be as pre ⁇ viously ' described for the first embodiment, although other powers may be selected, depending upon the speci ⁇ fic applications intended.
  • the lens body 61 or optic portion of the intraocular lens 60, is centered and retained within the eye by retaining means such as haptic members 64 and 65 having first ends 64a and 65a and second ends 64b and 65b, respectively.
  • the first ends 64a and 65a are cooperatively connected to the lens body 61 by methods well known in the art.
  • the construc- tion of a specific configuration of the haptic members 64 and 65 may be any suitable construction, such construction being well known in the art.
  • the haptic members 64 and 65, the first lens 62 and second lens 63 are molded as an integral one-piece structure.
  • the intraocular lens 60 may also be produced by other suitable methods such as forging and machining.
  • the unitary intraocular lens body 61, including the first lens 62 and second lens 63, is made of a biological tolerable and optically suitable material such as PMMA.
  • the haptic members 64 and 65 may be made of a flexible, compressible, resilient plastic material such as PMMA or polypropylene, or other materials as well known in the art.
  • the entire intraocular lens 60 is made of an integral one- piece structure and also is made of PMMA.
  • the intraocular lens 60 may serve as a bifocal vision system, with one lens 62 for reading and the other lens 63 for distant viewing .
  • bifocal vision systems such as bifocal glasses are exclusive. With the present embodiment this would not be the case.
  • One of the lens portions would have a focal length that is for viewing near objects and the other of the lens portions would have a focal length different from the first lens portion and that is for viewing distant objects.
  • Such a combination of lenses will produce two images on the retina which are superim ⁇ posed. Always, one of the two images will appear blurred, The eye is constantly scanning the images created on the retina and selectively chooses the image (the sharp one) to see.
  • the iris of the eye will always be in posi ⁇ tion in front of both lens portions 62 and 63 and there ⁇ fore the retina will always have an image formed on it from both the lens portions 62 and 63.
  • the area of the first lens portion 62 is preferably approximately equal to the area of the second lens portion 63.
  • chord 61a is substantially a diameter of the lens body 61.
  • the chord 61a could be offset from the center without departing from the invention.
  • the lens body 61 has a planar bottom surface 61b that extends across both the first lens portion 62 and second lens portion 63.
  • the first lens portion 62 has an upper convex sur ⁇ face 62a and the second lens portion 63 has an upper convex surface 63a, the latter one having a different radius of curvature than the first.
  • Reference numeral 66 generally indicates a transition region between the two lens portions which for the preferred embodiment shown, is chord 61a.
  • plane 67 represents a division of the lens 61 into its two halves 62 and 63 of different powers. While different radii of cur- vatures are drawn, the difference is small and hard to see. It will nevertheless be understood to be present.
  • Figure 7 is a cross-sectional view of a lens incorporating the present invention taken from a point of view generally analogous to the use for Figure 1, but showing an alternate thereto.
  • the lens body of Figure 7 is shown having a plano-convex structure. That is, it is generally planar on one side and convex on the other. This arrangement may be advantageous, in that it is potentially easier to construct.
  • the reference numeral 100 generally designates the eye, and the reference numeral 111 the lens.
  • the arrangement will be understood to be analogous to that shown in Figures 1-3, but for the utilization for a plano-convex structure for the lens.
  • the near vision portion 112 of the lens may be, for example, of the relative diameter to the distant vision portion 113, as previously described for Figures 1-3. In the alternative, that ratio of areas described previously for Figure 2A, may also, preferably, be used. Desirable corrective fac ⁇ tors for the two portions may be as previously indi ⁇ cated. That is, preferably, with the distance portion having a corrective power of between about +15 and +25 diopters, with the corrective power of the inner, near vision, lens portion having an add power of between about +2 and about +4 diopters.
  • Figure 8 a top plan view of the lens of Figure 7 is shown. Again, except for the plano-convex structure, the arrangement is analogous to that shown in Figure 2.
  • FIG 8A an alternate to the arrangement shown in Figure 7 and 8 is shown, wherein the inner lens portion 112' is constructed smaller, with respect to the outer lens portion 113'.
  • the annular portion have a diameter of about 6.0 to about 7.0 millimeters, while the inner portion has a diameter of about 1.8 to about 2.2 milli ⁇ meters.
  • the arrangement is generally analogous to that shown in Figure 2A, but for the plano-convex structure.
  • the preferred embodiment of the inven- tion is a bifocal lens, it should be understood that one or more additional lenses may be incorporated to correct for different distances.

Abstract

Une lentille intra-oculaire bifocale rigide (60) destinée à être utilisée comme un implant de lentille artificielle est décrite. Dans un mode de réalisation, la lentille intra-oculaire possède un corps rigide de lentille (61) ayant une ligne moyenne (61a) et des première et seconde portions de lentille (62 et 63). La première portion de lentille (61) possède une longueur focale et la seconde portion de lentille (634) possède une longueur focale différente de la longueur focale de la première portion de lentille (62). La première portion de lentille (62) est positionnée d'un côté de la ligne moyenne (61a) et la seconde portion de lentille (63) est positionnée du même côté de la ligne moyenne (61a). Les première et seconde portions de lentille (62 et 63) forment un corps de lentille optique intégrale en une seule pièce (61), les première et seconde portions de lentille n'étant pas amovibles l'une par rapport à l'autre. Dans un autre mode de réalisation, le corps rigide de lentille possède une première portion de lentille circulaire centrale et une seconde portion de lentille annulaire extérieure. Dans une forme préférentielle de ce mode de réalisation, la lentille circulaire interne possède un diamètre compris entre 1,8 millimètres environ et 2,2 millimètres environ, la portion de lentille annulaire extérieure ayant un diamètre compris entre 6 millimètres environ et 7 millimètres. Une puissance corrective préférée pour les lentilles utilisés dans les modes de réalisation décrits ci-dessus est comprise entre +15 environ et +25 dioptries pour une portion de lentille pour voir de loin, et une puissance corrective pour une portion de lentille pour voir de près d'une valeur de +2 à +4 dioptries supérieure à la puissance corrective de la portion de lentille pour voir de loin.
PCT/US1987/001284 1986-06-05 1987-06-03 Construction de lentille intra-oculaire bifocale en une seule piece WO1987007496A1 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US87107786A 1986-06-05 1986-06-05
US871,077 1986-06-05
US1587887A 1987-02-18 1987-02-18
US015,878 1987-02-18

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WO1987007496A1 true WO1987007496A1 (fr) 1987-12-17

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Cited By (34)

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WO1989009576A1 (fr) * 1988-04-15 1989-10-19 Schneider Richard T Structure de lentille intraoculaire bifocale en une seule piece
EP0419740A1 (fr) * 1989-09-27 1991-04-03 HANITA LENSES (a Limited Partnership) Lentille intra-oculaire de puissance négative
AU621108B2 (en) * 1988-05-11 1992-03-05 Laboratoires Domilens Anterior chamber intraocular implant
US5152787A (en) * 1990-12-19 1992-10-06 Eastman Kodak Company Intraocular gradient-index lenses used in eye implantation
US5166711A (en) * 1987-06-01 1992-11-24 Valdemar Portney Multifocal ophthalmic lens
US5166712A (en) * 1987-06-01 1992-11-24 Valdemar Portney Multifocal ophthalmic lens
US5225858A (en) * 1987-06-01 1993-07-06 Valdemar Portney Multifocal ophthalmic lens
US5270744A (en) * 1987-06-01 1993-12-14 Valdemar Portney Multifocal ophthalmic lens
EP0578739A1 (fr) * 1991-04-05 1994-01-19 Alcon Surgical, Inc., Lentille intra-oculaire avec correction de l'aberration spherique
US5344448A (en) * 1992-02-11 1994-09-06 Schneider Richard T Multi-focal intra-ocular implant
US5702440A (en) * 1996-01-26 1997-12-30 Allergan Multifocal ophthalmic lens for dim-lighting conditions
US5724258A (en) * 1996-05-09 1998-03-03 Johnson & Johnson Vision Products, Inc. Neural network analysis for multifocal contact lens design
US5864378A (en) * 1996-05-21 1999-01-26 Allergan Enhanced monofocal IOL or contact lens
US6210005B1 (en) 1999-02-04 2001-04-03 Valdemar Portney Multifocal ophthalmic lens with reduced halo size
US6231603B1 (en) 1998-11-10 2001-05-15 Allergan Sales, Inc. Accommodating multifocal intraocular lens
US8182531B2 (en) 2006-12-22 2012-05-22 Amo Groningen B.V. Accommodating intraocular lenses and associated systems, frames, and methods
US8465544B2 (en) 2006-12-29 2013-06-18 Abbott Medical Optics Inc. Accommodating intraocular lens
US8545556B2 (en) 2002-10-25 2013-10-01 Abbott Medical Optics Inc. Capsular intraocular lens implant
US8814934B2 (en) 2006-12-29 2014-08-26 Abbott Medical Optics Inc. Multifocal accommodating intraocular lens
US9005283B2 (en) 2004-04-16 2015-04-14 Visiogen Inc. Intraocular lens
US9011532B2 (en) 2009-06-26 2015-04-21 Abbott Medical Optics Inc. Accommodating intraocular lenses
US9039760B2 (en) 2006-12-29 2015-05-26 Abbott Medical Optics Inc. Pre-stressed haptic for accommodating intraocular lens
WO2015159111A1 (fr) 2014-04-18 2015-10-22 Medicontur Medical Engineering Ltd. Lentille intraoculaire secondaire ayant une partie optique coaxiale grossissante
US9198752B2 (en) 2003-12-15 2015-12-01 Abbott Medical Optics Inc. Intraocular lens implant having posterior bendable optic
US9271830B2 (en) 2002-12-05 2016-03-01 Abbott Medical Optics Inc. Accommodating intraocular lens and method of manufacture thereof
US9421089B2 (en) 2007-07-05 2016-08-23 Visiogen, Inc. Intraocular lens with post-implantation adjustment capabilities
US9504560B2 (en) 2002-01-14 2016-11-29 Abbott Medical Optics Inc. Accommodating intraocular lens with outer support structure
US9603703B2 (en) 2009-08-03 2017-03-28 Abbott Medical Optics Inc. Intraocular lens and methods for providing accommodative vision
US9636213B2 (en) 2005-09-30 2017-05-02 Abbott Medical Optics Inc. Deformable intraocular lenses and lens systems
US9814570B2 (en) 1999-04-30 2017-11-14 Abbott Medical Optics Inc. Ophthalmic lens combinations
US9968441B2 (en) 2008-03-28 2018-05-15 Johnson & Johnson Surgical Vision, Inc. Intraocular lens having a haptic that includes a cap
US9987125B2 (en) 2012-05-02 2018-06-05 Johnson & Johnson Surgical Vision, Inc. Intraocular lens with shape changing capability to provide enhanced accomodation and visual acuity
US10722400B2 (en) 2011-09-12 2020-07-28 Amo Development, Llc Hybrid ophthalmic interface apparatus and method of interfacing a surgical laser with an eye
US11707354B2 (en) 2017-09-11 2023-07-25 Amo Groningen B.V. Methods and apparatuses to increase intraocular lenses positional stability

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FR2510768A1 (fr) * 1981-07-29 1983-02-04 Lynell Med Tech Inc Construction de lentille intraoculaire et extraoculaire et procede pour sa fabrication
EP0140063A1 (fr) * 1983-09-07 1985-05-08 Manfred Dr. Achatz Lentille multifocale, particulièrement lentille bifocale intraoculaire artificielle
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US4010496A (en) * 1975-10-01 1977-03-08 Neefe Charles W Bifocal lens which positions within the anterior chamber
FR2510768A1 (fr) * 1981-07-29 1983-02-04 Lynell Med Tech Inc Construction de lentille intraoculaire et extraoculaire et procede pour sa fabrication
EP0140063A1 (fr) * 1983-09-07 1985-05-08 Manfred Dr. Achatz Lentille multifocale, particulièrement lentille bifocale intraoculaire artificielle
US4636211A (en) * 1984-03-13 1987-01-13 Nielsen J Mchenry Bifocal intra-ocular lens
WO1986003961A1 (fr) * 1984-12-31 1986-07-17 Antti Vannas Lentille intra-oculaire

Cited By (53)

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US5657108A (en) * 1987-06-01 1997-08-12 Portney; Valdemar Multifocal ophthalmic lens
US6814439B2 (en) 1987-06-01 2004-11-09 Valdemar Portney Multifocal ophthalmic lens
US5877839A (en) * 1987-06-01 1999-03-02 Portney; Valdemar Multifocal ophthalmic lens
US6527389B2 (en) 1987-06-01 2003-03-04 Advanced Medical Optics, Inc. Multifocal ophthalmic lens
US5166711A (en) * 1987-06-01 1992-11-24 Valdemar Portney Multifocal ophthalmic lens
US5166712A (en) * 1987-06-01 1992-11-24 Valdemar Portney Multifocal ophthalmic lens
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