EP4626362A1 - Lentille ophtalmique monofocale augmentée avec micro-perturbation de front d'onde - Google Patents

Lentille ophtalmique monofocale augmentée avec micro-perturbation de front d'onde

Info

Publication number
EP4626362A1
EP4626362A1 EP23898995.8A EP23898995A EP4626362A1 EP 4626362 A1 EP4626362 A1 EP 4626362A1 EP 23898995 A EP23898995 A EP 23898995A EP 4626362 A1 EP4626362 A1 EP 4626362A1
Authority
EP
European Patent Office
Prior art keywords
wavefront
perturbation
ophthalmic lens
lens
series
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.)
Pending
Application number
EP23898995.8A
Other languages
German (de)
English (en)
Inventor
Yueai Liu
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.)
Henan Simedice Biotechnologies Co Ltd
Henan Universe Intraocular Lens Research And Manufacture Co Ltd
Aaren Scientific Inc
Original Assignee
Henan Simedice Biotechnologies Co Ltd
Henan Universe Intraocular Lens Research And Manufacture Co Ltd
Aaren Scientific 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 Henan Simedice Biotechnologies Co Ltd, Henan Universe Intraocular Lens Research And Manufacture Co Ltd, Aaren Scientific Inc filed Critical Henan Simedice Biotechnologies Co Ltd
Publication of EP4626362A1 publication Critical patent/EP4626362A1/fr
Pending legal-status Critical Current

Links

Classifications

    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C7/00—Optical parts
    • G02C7/02—Lenses; Lens systems ; Methods of designing lenses
    • G02C7/024—Methods of designing ophthalmic lenses
    • G02C7/028—Special mathematical design techniques
    • 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
    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C7/00—Optical parts
    • G02C7/02—Lenses; Lens systems ; Methods of designing lenses
    • G02C7/022—Ophthalmic lenses having special refractive features achieved by special materials or material structures
    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C7/00—Optical parts
    • G02C7/02—Lenses; Lens systems ; Methods of designing lenses
    • G02C7/04—Contact lenses for the eyes
    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C2202/00—Generic optical aspects applicable to one or more of the subgroups of G02C7/00
    • G02C2202/12—Locally varying refractive index, gradient index lenses

Definitions

  • a cataract is a cloudy area in the eye's lens that leads to decreased vision. Cataracts often develop slowly and can affect one or both eyes, often leading to difficulty performing daily tasks such as driving, reading, or recognizing faces. If left untreated, cataracts may lead to blindness.
  • a common form of treatment is to remove the natural lens, called the crystalline lens, and replace it with a prosthetic lens called an intraocular lens (IOL).
  • IOL intraocular lens
  • An IOL can be designed to provide an excellent visual acuity for a single focal point or for several focal points.
  • the former is referred to as a monofocal IOL and generally uses an aspheric surface.
  • the latter is referred to as a multifocal IOL and uses a diffractive surface.
  • a multifocal IOL having more than one focal point, is often preferred over a monofocal IOL as such lenses generally eliminate the need for glasses.
  • multifocal lenses are more expensive than monofocal lenses because of their diffractive design, and patients using multifocal lenses are many times less satisfied with their vision experience than patients using monofocal lenses.
  • many IOL monofocal designs seek to improve the depth of focus at the lens’s single focal point by modifying its aspherical surface.
  • Extended depth of focus intraocular lens which discloses an IOL that comprises an optic zone and a modulated surface profile formed in the optic zone and configured to focus incident light at a plurality of focal points, wherein the modulated surface profile is incorporated with a base surface profile of the optic zone.
  • the modulated surface may have a profile that is sinusoidal, triangular, or some form thereof, the purpose of which is to extend the depth of focus.
  • Another example is United States patent 11083566 to Xin Hong et al. titled “Ophthalmic lens having an extended depth of focus.” Here, Hong discloses an ophthalmic lens that includes an optic having an anterior surface, a posterior surface, and an optical axis.
  • At least one of the anterior surface and the posterior surface includes a first zone extending from the optical axis to a first radial boundary and a second zone extending from the first radial boundary to the edge of the optic.
  • the first zone includes an inner region and an outer region separated by a phase shift feature, the phase shift comprising a ridge extending outwardly from the inner region and the outer region.
  • the optical combination of the inner region, phase shift feature, and outer region of the first zone and the second zone extends the depth of focus of the lens.
  • an ophthalmic lens such as spectacle glasses, contacts, or intraocular lenses having an optic that is generally monofocal but having a zone about the central paraxial region where a wavefront perturbation has been added.
  • the wavefront perturbation could be realized with surface relieving on either the anterior and posterior surfaces of the lens or with refractive index modification of the lens material at some depth inside of the optic.
  • the object of the wavefront perturbation is to extend the depth of focus that may correct the presbyopia of the wearer under photopic conditions at all distances. Under mesopic vision, the lens becomes monofocal-like.
  • FIG.2 shows monofocal ophthalmic lens 10, the wavefront emerging from the lens is largely a sphere that converges to a single focal point, shown as 14 in FIG.2.
  • Lens 10 through focus Modulation Transfer Function (MTF) is shown as 16.
  • MTF focus Modulation Transfer Function
  • Light converging at focal point 14 may be said to be emmetropia vision. It is desirable for a presbyopia or a pseudophakia patient who wears lens 10 to have a monofocal through focus MTF 16 that is wider, representing a greater depth of focus extending from the emmetropia focus toward the myopia direction.
  • FIG.3 shows augmented monofocal ophthalmic lens 20 having a central paraxial region 26 of the present disclosure.
  • Paraxial region 26 contains a wavefront perturbation that diffracts the wavefront emerging from lens 20 and splits it into numerous sub-wavefronts, allowing the incoming light energy to be distributed to a depth of focus from focal point 14 in the myopia direction. As a result, the width of through focus MTF 16 is increased, thereby its depth of focus.
  • Such a wavefront-perturbed ophthalmic lens would let a presbyopia or pseudophakia wearer gain a pseudo accommodation function and see clearly within the depth of focus of the lens under photopic conditions. What is disclosed herein is a monofocal ophthalmic lens 20 having perturbation within paraxial region 22.
  • the perturbation is a continuous even function of the radius of paraxial region 22 and is rotationally symmetrical about the optical axis of lens 20.
  • Other features and advantages of various embodiments of the present invention will be apparent to one skilled in the art from the following description.
  • BRIEF DESCRIPTION OF DRAWINGS The present invention will become more fully understood from the detailed description and accompanying drawings.
  • Other systems, methods, features, and advantages of the invention will be or will become apparent to one with skill in the art upon examination of the following figures and detailed description. It is intended that all such additional systems, methods, features, and advantages be included within this description, be within the scope of the invention, and be protected by the accompanying claims.
  • Component parts shown in the drawings are not necessarily to scale and may be exaggerated to better illustrate the important features of the invention.
  • FIG.1 shows the augmented monofocal ophthalmic lens of the present disclosure having a central paraxial region containing a micro wavefront perturbation
  • FIG.2 shows how a monofocal ophthalmic lens of the prior art functions
  • FIG.3 shows how the augmented monofocal ophthalmic lens of the present disclosure functions
  • FIG.4 shows the surface profile of a first embodiment where the perturbation is expressed as a cosine series
  • FIG.5 shows the through focus MTF of a first embodiment where the perturbation is expressed as a cosine series.
  • FIG.6 shows the surface profile of a second embodiment where the perturbation is expressed as a cosine series
  • FIG.7 shows the through focus MTF of a second embodiment where the perturbation is expressed as a cosine series.
  • FIG.8 shows the surface profile of a third embodiment where the perturbation is expressed as a Fourier harmonic series;
  • FIG.9 shows the through focus MTF of a third embodiment where the perturbation is expressed as a Fourier harmonic series.
  • FIG.10 shows the surface profile of a fourth embodiment where the perturbation is expressed as a Fourier harmonic series;
  • FIG.11 shows the through focus MTF of a fourth embodiment where the perturbation is expressed as a Fourier harmonic series.
  • FIG.12 shows the surface profile of a fifth embodiment where the perturbation is expressed as a Fourier harmonic series
  • FIG.13 shows the through focus MTF of a fifth embodiment where the perturbation is expressed as a Fourier harmonic series.
  • the exemplary embodiments relate to ophthalmic devices such as spectacle glasses, IOLs, and contact lenses.
  • the following description is presented to enable one of ordinary skill in the art to make and use the invention and is provided in the context of a patent application and its requirements. Modifications to the exemplary embodiments and the generic principles and features described herein will readily be apparent.
  • the exemplary embodiments are mainly described in terms of particular methods and systems provided in particular implementations. However, the methods and systems will operate effectively in other implementations.
  • FIG.1 shows lens 20, being an augmented monofocal lens of the present disclosure, as an IOL comprising optic 22 and haptics 24 and further comprising paraxial region 26 about the optical axis and monofocal region 28 from the extent of paraxial region 26 to the edge of optic 22.
  • the radius of paraxial region 26, R 0 is shown as a dashed line in FIG.1.
  • the wavefront perturbation could be realized with surface relieving on either the anterior and posterior surfaces of optic 22 or with refractive index modification of the material within optic 22.
  • the objective of the wavefront perturbation is to extend the depth of focus that may correct the presbyopia of the wearer under photopic conditions at all distances from far to near continuously.
  • the perturbation of the wavefront at either the anterior and posterior surfaces of the optic or with refractive index modification of the lens material at some depth inside the optic is a continuous even function of the radius of the aperture of the wavefront. Therefore, it is also rotationally symmetrical about the optical axis and is continuously differentiable within paraxial region 26.
  • the wavefront of the augmented monofocal lens ⁇ ( ⁇ ) consists of two parts, the one is the base monofocal wavefront, ⁇ ( ⁇ ); the other is ⁇ ( ⁇ ), the perturbation wavefront. This is expressed in Eq. (1).
  • ⁇ ( ⁇ ) ⁇ ( ⁇ ) + ⁇ ( ⁇ ) Eq. (1)
  • the perturbation part of the wavefront is confined within the paraxial region 26 that has a radius of ⁇ ⁇ .
  • the probation is a constant ⁇ , as is shown in Eq. (3).
  • R is the radius of the lens aperture
  • ⁇ ⁇ is the radius of the aperture of the perturbation as is shown in FIG.1
  • r is the distance from the optical axis
  • ⁇ ( ⁇ ) is a continuous even function of ⁇ .
  • ⁇ ( ⁇ ) must be parameterized.
  • Optimal wavefront perturbations expressed as a cosine series would have N in the range of 3 ⁇ ⁇ ⁇ 10, ⁇ ⁇ in the range of 0.5 ⁇ ⁇ ⁇ ⁇ 2 ⁇ , and ⁇ ⁇ the range of ⁇ 0.5 ⁇ ⁇ ⁇ ⁇ 0.5.
  • the following paragraphs discloses two embodiments of the wavefront perturbation expressed as a cosine series.
  • the first embodiment of the wavefront perturbation, expressed as a cosine series has the parameters shown in Table 1.
  • Table 1 Parameters for the second embodiment of the wavefront perturbation, expressed as a cosine series.
  • R 0 is measured in millimeters, the coefficients of the cosine series are measured in waves.
  • FIG.4 shows the resulting wavefront perturbation sag for the first embodiment on the surface of optic 22, with the x-axis being the surface of optic 22 and the y-axis being the height of the sag.
  • the optical axis of optic 22 is at 0.0 mm on the x-axis.
  • the perturbed wavefront sag is horizontal outside of R 0 , where R 0 is the radius of paraxial region 26, as shown in FIG.1.
  • the through focus MTF is shown for the perturbed wavefront of the first embodiment at a 3 mm aperture, or pupil size of the eye.
  • the solid line shows the through focus MTF at 25 cycles per millimeter (CPMM), while the dashed line shows the through focus MTF at 50 CPMM.
  • CPMM cycles per millimeter
  • the second embodiment of the wavefront perturbation also expressed as a cosine series, has the parameters shown in Table 2.
  • Table 2 Parameters for the second embodiment of the wavefront perturbation, expressed as a cosine series.
  • FIG.6 shows the resulting wavefront perturbation sag for the second embodiment on the surface of optic 22, with the x-axis being the surface of optic 22 and the y-axis being the height of the sag.
  • the optical axis of optic 22 is at 0.0 mm on the x-axis.
  • the perturbed wavefront sag is horizontal outside of R 0 , where R 0 is the radius of paraxial region 26, as shown in FIG.1.
  • the through focus MTF is shown for the perturbed wavefront of the second embodiment at a 3 mm aperture.
  • the solid line shows the through focus MTF at 25 cycles per millimeter (CPMM), while the dashed line shows the through focus MTF at 50 CPMM. Comparing the through focus MTF from FIG.7 with monofocal through focus MTF 16 in FIG.2, it may be seen that the wavefront perturbation of the second embodiment has an expanded depth of focus as compared to the prior art monofocal lens shown in FIG.2.
  • the wavefront perturbation function ⁇ ( ⁇ ) may also be expressed as a Fourier harmonics series as indicated in Eq. (6).
  • ⁇ ⁇ ⁇ ( ⁇ ) ⁇ ⁇ ⁇ ⁇ + ⁇ ( ⁇ ⁇ cos( ⁇ ⁇ ) + ⁇ ⁇ sin( ⁇ ⁇ ))
  • ⁇ is an integer indicating the order of the Fourier harmonic series; ⁇ is the wavelength of incident light; and r is the distance from the optical axis.
  • the cosine wavefront perturbation there exists a range of values for each design parameter of the Fourier series wavefront perturbation.
  • ⁇ ⁇ is in the range of 0.5 ⁇ ⁇ ⁇ ⁇ 2.5 ⁇ ; ⁇ is in the range of 1 ⁇ ⁇ ⁇ 3, ⁇ is in the range of 5 ⁇ ⁇ ⁇ 15, ⁇ ⁇ is in the range of ⁇ 0.5 ⁇ ⁇ ⁇ ⁇ 0.5, and ⁇ ⁇ is in the range of ⁇ ⁇ ⁇ ⁇ ⁇ ⁇ .
  • ⁇ ⁇ 0.56 ( ⁇ ⁇ )
  • ⁇ 1.083 ( ⁇ ) while Table 3 contains the Fourier harmonic parameters.
  • Table 3 The Fourier harmonic parameters for the third embodiment of the wavefront perturbation. ⁇ ⁇ ⁇ ( ⁇ ) ⁇ ⁇ - 3 0.03800426 -1.45079958 4 -0.02373634 1.55496512 5 0.02734461 -0.57577025 6 0.03739066 -1.51366902 7 -0.01797941 1.55055861 8 -0.01337226 1.60851219 9 0.00841704 -1.02274817 10 -0.01114590 1.62044934 11 -0.00712054 1.04770549 12 0.00978682 0.00000000
  • FIG.8 shows the resulting wavefront perturbation sag for the third embodiment on the surface of optic 22, with the x-axis being the surface of optic 22 and the y-axis being the height of the sag.
  • the optical axis of optic 22 is at 0.0 mm on the x-axis.
  • the perturbed wavefront sag is horizontal outside of R 0 , where R 0 is the radius of paraxial region 26, as shown in FIG.1.
  • the through focus MTF is shown for the perturbed wavefront of the third embodiment at a 3 mm aperture.
  • the solid line shows the through focus MTF at 25 cycles per millimeter (CPMM), while the dashed line shows the through focus MTF at 50 CPMM. Comparing the through focus MTF from FIG.9 with monofocal through focus MTF 16 in FIG.2, it may be seen that the wavefront perturbation of the third embodiment has an expanded depth of focus as compared to the prior art monofocal lens shown in FIG.2.
  • Table 4 The Fourier harmonic parameters for the fourth embodiment of the wavefront perturbation.
  • FIG.10 shows the resulting wavefront perturbation sag for the fourth embodiment on the surface of optic 22, with the x-axis being the surface of optic 22 and the y-axis being the height of the sag.
  • the optical axis of optic 22 is at 0.0 mm on the x-axis.
  • the perturbed wavefront sag is horizontal outside of R 0 , where R 0 is the radius of paraxial region 26, as shown in FIG.1.
  • the through focus MTF is shown for the perturbed wavefront of the fourth embodiment at a 3 mm aperture.
  • the solid line shows the through focus MTF at 25 cycles per millimeter (CPMM), while the dashed line shows the through focus MTF at 50 CPMM. Comparing the through focus MTF from FIG.11 with monofocal through focus MTF 16 in FIG.2, it may be seen that the wavefront perturbation of the fourth embodiment has an expanded depth of focus as compared to the prior art monofocal lens shown in FIG.2.
  • Table 5 The Fourier harmonic parameters for the fifth embodiment of the wavefront perturbation.
  • FIG.12 shows the resulting wavefront perturbation sag for the fifth embodiment on the surface of optic 22, with the x-axis being the surface of optic 22 and the y-axis being the height of the sag.
  • the optical axis of optic 22 is at 0.0 mm on the x-axis.
  • the perturbed wavefront sag is horizontal outside of R 0 , where R 0 is the radius of paraxial region 26, as shown in FIG.1.
  • the through focus MTF is shown for the perturbed wavefront of the fifth embodiment at a 3 mm aperture.
  • the solid line shows the through focus MTF at 25 cycles per millimeter (CPMM), while the dashed line shows the through focus MTF at 50 CPMM. Comparing the through focus MTF from FIG.13 with monofocal through focus MTF 16 in FIG.2, it may be seen that the wavefront perturbation of the fifth embodiment has an expanded depth of focus as compared to the prior art monofocal lens shown in FIG.2.
  • the wavefront perturbation function ⁇ ( ⁇ ) may also be expressed as even Zernike polynomials as indicated in Eq. (10). ⁇ Eq.
  • ⁇ ( ⁇ ) ⁇ ⁇ ⁇ ⁇ ⁇ ⁇ ( ⁇ , ⁇ )
  • r and ⁇ are the radial and azimuth polar coordinates on the lens aperture
  • r is the radius of the lens aperture
  • n and m are integer variables indicating the radial and azimuth order of the polynomials
  • ⁇ ⁇ ⁇ are the corresponding coefficients
  • the rotational Zernike polynomial wavefront perturbation in Eq. (13) is effectively the same as the Taylor series in Eq. (9).
  • the wavefront perturbation expressed in Eq. (13) may make the engineering design converge faster to the optimal wavefront perturbation for the desired IOL performance.
  • both the cosine series and Fourier harmonic series types of wavefront perturbations can also be expressed in the form of Taylor series, and hence, Zernike polynomials.

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  • Health & Medical Sciences (AREA)
  • Ophthalmology & Optometry (AREA)
  • Physics & Mathematics (AREA)
  • General Health & Medical Sciences (AREA)
  • Optics & Photonics (AREA)
  • General Physics & Mathematics (AREA)
  • Vascular Medicine (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Biomedical Technology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Engineering & Computer Science (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Transplantation (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Cardiology (AREA)
  • Mathematical Physics (AREA)
  • Eyeglasses (AREA)

Abstract

L'invention concerne une lentille ophtalmique monofocale, dont les performances sont augmentées pour la correction de la presbytie, ayant un front d'onde qui est modifié avec une perturbation au niveau de sa région paraxiale centrale. La perturbation peut être réalisée par soulagement de surface sur ses surfaces antérieure ou postérieure ou par modification de l'indice de réfraction du matériau de lentille. La perturbation se présente sous la forme d'une fonction régulière telle que, mais de façon non limitative, un cosinus, des harmoniques de Fourier, des polynômes de Zemike, ou une série de Taylor par rapport au rayon de l'ouverture de front d'onde.
EP23898995.8A 2022-12-02 2023-12-01 Lentille ophtalmique monofocale augmentée avec micro-perturbation de front d'onde Pending EP4626362A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US202263385800P 2022-12-02 2022-12-02
PCT/US2023/082074 WO2024119071A1 (fr) 2022-12-02 2023-12-01 Lentille ophtalmique monofocale augmentée avec micro-perturbation de front d'onde

Publications (1)

Publication Number Publication Date
EP4626362A1 true EP4626362A1 (fr) 2025-10-08

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Application Number Title Priority Date Filing Date
EP23898995.8A Pending EP4626362A1 (fr) 2022-12-02 2023-12-01 Lentille ophtalmique monofocale augmentée avec micro-perturbation de front d'onde

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EP (1) EP4626362A1 (fr)
CN (1) CN119343108A (fr)
WO (1) WO2024119071A1 (fr)

Family Cites Families (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
SE0004829D0 (sv) * 2000-12-22 2000-12-22 Pharmacia Groningen Bv Methods of obtaining ophthalmic lenses providing the eye with reduced aberrations
KR102171529B1 (ko) * 2014-09-09 2020-10-30 스타 서지컬 컴퍼니 확장된 피사계 심도 및 향상된 원거리 시력의 안과용 임플란트
EP3130314A1 (fr) * 2015-08-12 2017-02-15 PhysIOL SA Lentille intraoculaire à triple foyer avec une plage étendue de la vision et de la correction d'aberration chromatique longitudinale
US11083566B2 (en) * 2016-02-29 2021-08-10 Alcon Inc. Ophthalmic lens having an extended depth of focus
US9993336B2 (en) * 2016-06-06 2018-06-12 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods
DE102017007990B4 (de) * 2017-01-27 2023-01-19 Rodenstock Gmbh Computerimplementierte Verfahren und Vorrichtungen zum Ermitteln individueller Aberrationsdaten oder zum Berechnen oder Optimieren eines Brillenglases für zumindest ein Auge eines Brillenträgers, Computerimplementiertes Verfahren zum Ermitteln optimierter sphärozylindrischer Werte für zumindest ein Auge eines Brillenträgers, Verfahren und Vorrichtung zum Herstellen eines Brillenglases, Brillengläser und Computerprogrammerzeugnis
WO2020132703A1 (fr) * 2018-12-20 2020-06-25 Aaren Scientific Inc. Lentille intraoculaire diffractive quintafocale
CA3169919A1 (fr) * 2020-04-16 2021-10-21 Myoung-Taek Choi Lentilles ophtalmiques ayant une profondeur de foyer etendue pour ameliorer la vision intermediaire
CA3208746A1 (fr) * 2021-02-19 2022-08-25 Vsy Biyoteknoloji Ve Ilac Sanayi A.S. Lentille oculaire diffractive multifocale adaptative

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Publication number Publication date
WO2024119071A1 (fr) 2024-06-06
CN119343108A (zh) 2025-01-21

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