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EP4655640A1 - Lentille oculaire diffractive quadrifocale - Google Patents

Lentille oculaire diffractive quadrifocale

Info

Publication number
EP4655640A1
EP4655640A1 EP22917631.8A EP22917631A EP4655640A1 EP 4655640 A1 EP4655640 A1 EP 4655640A1 EP 22917631 A EP22917631 A EP 22917631A EP 4655640 A1 EP4655640 A1 EP 4655640A1
Authority
EP
European Patent Office
Prior art keywords
lens
vision
diffractive
order
orders
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
EP22917631.8A
Other languages
German (de)
English (en)
Inventor
Sven Thage Sigvard HOLMSTRÖM
Amin TABATABAEI MOHSENI
Efe CAN
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.)
VSY Biyoteknoloji ve Ilac Sanayi AS
Original Assignee
VSY Biyoteknoloji ve Ilac Sanayi AS
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 VSY Biyoteknoloji ve Ilac Sanayi AS filed Critical VSY Biyoteknoloji ve Ilac Sanayi AS
Publication of EP4655640A1 publication Critical patent/EP4655640A1/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
    • G02C7/04—Contact lenses for the eyes
    • G02C7/041—Contact lenses for the eyes bifocal; multifocal
    • G02C7/042—Simultaneous type
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/14—Eye parts, e.g. lenses or corneal implants; Artificial eyes
    • A61F2/16—Intraocular lenses
    • A61F2/1613—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • A61F2/1654—Diffractive lenses
    • 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
    • G02C2202/20—Diffractive and Fresnel lenses or lens portions

Definitions

  • the present disclosure generally relates to ophthalmic lenses as well as to ophthalmic contact and intra-ocular multifocal lenses, more specifically lenses where the multifocality is provided by a smooth diffractive structure without discontinuities that is arranged to provide four diffraction orders in a way best serve human vision over different pupil sizes under various light conditions.
  • Diffractive lenses for ophthalmological applications are constructed as hybrid lenses with a diffractive pattern added onto a refractive body. Often one side of the lens is purely refractive, while the other side has a diffractive grating superpositioned over a refractive base line.
  • the refractive baseline can be spherical, or alternatively have an aspherical shape.
  • the diffractive part can in general be applied to any of the two sides of the lens, since when a diffractive pattern is to be combined with a refractive surface with some special feature it generally does not matter if they are added to the same side or if one is added to a first side and the other to a second side of the lens.
  • two diffractive patterns may be combined either by super positioning on one side, or by adding them on separate sides in an overlapping fashion.
  • the optical power of the lens for a specific diffraction order can be calculated by addition of the refractive base power and the optical power of that diffraction order.
  • the most well-researched type of diffraction lens proper is the monofocal phase-matched Fresnel lens as taught by Rossi et al. in their 1995 study titled "Refractive and diffractive properties of planar micro-optical elements".
  • This type of lens makes use of a sawtooth diffractive unit cell and a step height corresponding to a phase modulation of exactly 2n.
  • Most multifocal lenses with more than two foci still use a configuration where the 0 th order is utilized to provide far vision to the user akin to the case in sawtooth diffractive gratings, due to it being relatively easier to design a lens that provides high quality vision at the 0 th order.
  • Far vision is usually prioritized, especially for intraocular lenses as surgical success is usually determined by the functionality of far vision.
  • Such gratings can be either trifocal or bifocal, depending on the height of the structure.
  • Symmetric sinusoidal diffractive gratings i.e. sinusoidal diffractive gratings that have their orders evenly arranged around the 0 th order are the most lightefficient gratings possible for diffractive lenses with an odd number of usable focal points, they avoid sharp transitions in the diffractive profile, increase manufacturability, and biocompatibility. The latter point is originally suggested in Osipov et al. in their 2015 study "Application of nanoimprinting technique for fabrication of trifocal diffractive lens with sine-like radial profile" as published in Journal of biomedical optics 2 , no. 2 (2015): 025008.
  • Diffractive profiles without discontinuities have several very important advantages: They are less prone to produce undesired photic phenomena, such as halo and glare and other positive dysphotopsias, they are cheaper to manufacture well, they open up a wider set of manufacturing techniques, and they allow for continuous tuning of the light intensity distribution on a subperiod scale. For symmetric trifocal and pentafocal (lenses providing five diffraction orders) lenses this has been discussed in detail in W02019020435A1 and WO2022177517A1.
  • Asymmetric diffractive lenses that is lenses with a different number of usable orders on each side of the 0 th order can be advantageous.
  • the asymmetric diffractive gratings have a smaller relative difference in power between the 0 th order and the order used for far vision, which can be used as an advantage.
  • Having a far power closer to the zeroth order e.g. decreases undesired diopter offset in autorefractometry measurements, and the chromatic aberration caused by diffraction can be chosen to be smaller than in a lens with a symmetric grating.
  • a sawtooth-like asymmetric diffractive lens is exemplified in WO2021245506.
  • Symmetric sinusoidal, continuous diffractive multifocal lenses can be found in the literature.
  • W02019020435A1 discloses a multifocal lens comprising a diffraction grating designed to operate as an optical wave splitter for distributing light incident at said lens body in said refractive and diffractive focal points.
  • Said diffraction grating has an optical transfer function comprising a continuous periodic phase profile function extending in radial direction of the lens body.
  • Said continuous periodic phase profile function also comprises an argument modulated as a function of radial distance to said optical axis of said lens body, thereby tuning said distributing of light incident at said lens body.
  • WO2022177517A1 discloses an ophthalmic multifocal lens with a light transmissive body with an optical axis and a refractive baseline extending over part of the body of the lens. It also discloses a first portion coinciding with a central area of said lens body and a multifocal second portion extending concentrically radially; said second portion further comprising a symmetric multifocal diffractive grating superpositioned onto said baseline, covering a portion of the lens, its shape and resulting light intensity distribution changing with distance to optical axis.
  • this disclosure describes aperture- adaptive diffractive lenses with greater light efficiency and higher effective efficiency due to better adaption to the anatomy of the eye.
  • each period of the diffraction individually to provide at each aperture (and corresponding pupil size) the desired intensity distribution between e.g. far, intermediate, and near vision.
  • asymmetric lenses it would be desired to be able to be able to create multifocal lenses with asymmetric diffractive gratings with usable orders on both sides of the zeroth order while retaining the advantages of the known sinusoidal lenses.
  • US10993798B2 presents a multifocal diffractive lens with a sawtooth pattern utilizing four consecutive diffraction order, of which one of the two middle orders is suppressed.
  • WO2021245506 teaches a lens with what possibly is a diffractive profile with four diffraction orders, and at least one on each side of the zeroth order, even if this is not explicitly claimed.
  • the presented diffractive profile makes use of a sharp vertical jump.
  • the document only discusses three usable focal points, for far, intermediate, and near, respectively.
  • a lens to provide vision enough for a user to be spectacle independent it needs to provide far, intermediate, and near vision.
  • far vision In photopic conditions, when small pupils are present a full multifocal vision with an especially strong far vision is desired. But a central aperture of the lens that provides a very narrow far vision runs an increased risk of diopter mismatch. A central portion of the lens providing slightly stronger power than the intended power of far vision will decrease this risk. This is especially important since quality of the far vision is indeed what determines clinical success of cataract surgery.
  • Multifocal ophthalmic lenses are often optimized to provide vision at two or three distances, arranged to coincide with far, intermediate, and near vision. This is mostly due vision being measured clinically at these specific distances. However, for the wellbeing of patients, especially those who want to be spectacle free, it is often better to provide more continuous vision.
  • W02020053864 presents a lens using a symmetric grating providing five focal points, where the highest and the lowest orders together with the central order correspond with the far, intermediate, and near, and the two remaining orders provide some continuous vision.
  • an improved ophthalmic lens that utilizes the advantages of smooth diffractive gratings without discontinuities, with usable orders on both sides of the zeroth order, including very high light efficiency, fewer diffractive rings, and the possibility to have biologically and manufacturing-wise more suitable diffractive profiles in a way that allows for exact placement of the dominant optical power for any aperture, allows for aperture dependent tuning of light intensity distribution; and combining these features with asymmetric diffractive gratings having usable diffractive orders on both sides of the zeroth order that are able to more precisely distribute intermediate light with respect to pupil size.
  • Primary object of the present invention is to provide an ophthalmic multifocal lens, comprising a refractive baseline, an optical axis and providing at least four focal points, one of them providing far vision to a user.
  • Another object of the present invention is to provide an ophthalmic multifocal lens that provides far vision in a configuration using a diffractive order other than the 0 th order, while retaining a high quality comparable to configurations that use the 0 th order to provide far vision.
  • a further object of the present invention is to provide an ophthalmic multifocal lens comprising a smooth diffractive grating without discontinuities that has a lowest diffractive order that provides far vision, a highest diffractive orders that provides near vision and two middle diffractive order that contribute to intermediate vision or provide increased continuous vision.
  • a still further object of the present invention is to provide an ophthalmic multifocal lens wherein said diffractive grating has an aperture-dependent intensity distribution such that the higher order of the two middle diffractive orders provides the higher light intensity of the two to a user at a lens aperture of 3 mm, while the lower of the two middle orders provides the higher light intensity to a user at some higher lens aperture.
  • an ophthalmic multifocal lens at least comprising a focal point for far vision.
  • the lens having a light transmissive lens body comprising a diffraction grating having useful diffraction orders on both sides of the zeroth order extending concentrically in a radial direction from an optical axis of the lens body across a part of a surface of the lens body.
  • the diffraction grating is configured such that the diffraction orders make use of the following orders: -1, 0, +1, and +2.
  • lens comprises at least a refractive baseline.
  • a well-formed diffractive lens has, as known in the art, a pitch that in absolute terms (i.e. measured in millimeters) varies with the radius, however is constant in quadratic (r 2 ) space.
  • Lenses manufactured according to the present disclosure have at least four focal points and make use of a diffraction grating that at the very least lack discontinuities for the innermost three diffractive rings.
  • the -1 st order of the diffraction grating is arranged to correspond to far vision, whereas the +2 nd order is arranged to provide near vision for a user.
  • Said quadrifocal lens can be tuned in several ways for achieving different types of multifocal lenses. It is possible to choose between several main configurations that differ in for which distances continuous vision can be provided. Additionally, the intensity distribution of each main configuration can be tuned as a function of the lens aperture by changing the diffractive unit cell as a function of the lens aperture. For larger apertures, relevant in scotopic environments, it is often preferable to shift light away from near vision and more distant intermediate vision towards far vision (order -1) or to the zeroth order.
  • One important feature in the present disclosure is a shoulder structure facing towards the center of the lens in one unit cell. This feature is often advantageously used to spread light to three or four focal points. For parts of the lens, such as the periphery where more far vision is desired, this feature can be less prominent.
  • Present disclosure additionally offers a feature for a further improvement in means of the configuration of the sinusoidal, or smooth, quadrifocal grating that places a lowest intensity point between the -1 st and the 0 th orders.
  • This creates a configuration of very suitable ophthalmic lenses for users who want to lead spectacle-free life.
  • the lens configuration comprising said feature as such provides a strong far vision and also utilizes light provided to near vision, intermediate vision and further.
  • Overall, for 2 mm and for 3 mm lens apertures a very high degree of continuous vision for the whole range of far to near vision is achieved. For larger apertures, more light intensity goes into far vision, as desired.
  • Figure 1 demonstrates a simplified anatomy of the human eye.
  • Figures 2a and 2b demonstrate a front and side view, respectively, of an ophthalmic multifocal aphakic intraocular lens as known in the art.
  • Figures 3a and 3b demonstrate a front and side view, respectively, of an ophthalmic multifocal aphakic intraocular lens made according to the present invention.
  • Figures 4a, 4b, and 4c demonstrate the surface profiles, less the respective refractive baseline, of three quadrifocal lenses made according to the present invention.
  • Figures 4d, 4e, and 4f demonstrate the modelled relative intensity of the diffractive profiles in Figures 4a, 4b, and 4c, respectively.
  • Figures 5a and 5b demonstrate, respectively, the profile, less the refractive baseline, and the modelled relative intensity graph of another diffractive lens made according to the patent.
  • Figures 5c and 5d demonstrate, respectively, the profile, less the refractive baseline, and the modelled relative intensity graph of another diffractive lens made according to the patent. Detailed Description of the Present Invention
  • diffractive gratings One important property of diffractive gratings is the distinction between symmetric and asymmetric diffraction gratings. When ascribing symmetric or asymmetric property to multifocal ophthalmic lenses, what is considered is which diffraction orders it makes use of or renders useful. Symmetric diffractive lenses utilize orders in a way that is symmetric around the 0 th order. Note that symmetric diffraction gratings are defined by which orders they utilize, not by the intensity of light distribution in these orders. Some symmetric diffractive lenses may be tuned so that there is a significant difference in light intensity between e.g., +1 and -1 orders, i.e. they have an unequal light distribution.
  • a diffraction grating tuned as such would still be considered a symmetric diffraction grating.
  • Lenses based on symmetric gratings can be trifocal, making use of order -1, 0, and +1, or pentafocal, making use of order -2, -1, 0, +1, and +2.
  • Such symmetric gratings can be sinusoidal or non-sinusoidal.
  • a commonly known non-sinusoidal symmetric grating is the binary grating.
  • gratings not making use of the 0 th order can also be considered symmetric.
  • the symmetric case of a grating making use of the four order -2, -1, +1, and +2 can, in some cases, be useful for ophthalmic lenses.
  • the highest possible diffraction efficiency for most useful intensity distribution for diffractive multifocal lenses with an odd number of foci, including trifocal lenses, is provided by smooth sinusoidal surfaces with usable orders symmetrically arranged around the 0 th order.
  • Diffraction efficiency is a measure of how much of the optical power is directed into the desired diffraction orders, or, when referring to diffractive lenses in particular, how much of the optical power is directed into the desired focal points.
  • Diffraction efficiency is a measure of how much of the optical power is directed into the desired diffraction orders, or, when referring to diffractive lenses in particular, how much of the optical power is directed into the desired focal points.
  • the highest possible diffraction efficiency is reached by using the principles of a phase- matched Fresnel lens, which makes use of a sawtooth or jagged type diffraction pattern.
  • any such linear phase can be turned into a lens.
  • This optimization theory is one of several good ways to find a way to start developing a lens grating.
  • optimizing for the highest diffraction efficiency is not always the best option for a diffractive unit cell to be used in a grating, there are important effects specific for lenses not taken into account by optimization of linear phase gratings, optimizing for these effects can be advantageous when designing lenses according to the present invention.
  • the lens according to the present invention is an ophthalmic lens comprising at least a refractive baseline and a diffractive grating super positioned on to the refractive baseline, arranged so that, for a design wavelength, orders on both sides of the 0 th order are made usable for a user of the lens.
  • a strong far vision is the typical criterion to ascertain the success of cataract surgery. This is because a strong far vision is important for all apertures.
  • the apertures and pupil sizes that are all defined in the anterior lens plane, assuming an average human eye. But to be clear, the corresponding pupil sizes are larger, the exact sizes of which will differ slightly from person to person.
  • a 2 mm aperture in the lens plane corresponds to a 2.35 mm pupil diameter
  • 3 mm in the lens plane corresponds to 3.515 mm, 4.5 mm to 5.28 mm, and 6 mm to 7.04 mm.
  • One important aspect of the present invention is tuning the intensity distribution as a function of the lens aperture.
  • the eye has a much larger depth of field at pupil sizes that are smaller, due to the pinhole effect.
  • Pupil size not being solely dependent on the pupillary light reflex, is also dependent on the accommodation reflex, which causes the pupil to enlarge insufficiently while focusing on objects of closer proximity. Due to this, it often advantageous to shift light from near vision to far vision for pupil sizes that are large, while also prioritizing intermediate vision over near vision for larger apertures, and even further removing or spreading light from near vision for cases when light cannot be redistributed to other usable gratings.
  • the pinhole effect is important to consider.
  • a constriction of the pupil increases the depth of focus of the lens, for tiny pupils this effect generally provides a relatively good vision at all distances even with a lens that is providing only a single focus.
  • Many modern multifocal- and enhanced depth- of-focus (EDOF) lenses takes advantage of this effect by allowing the light provided by the lens to be dominated by intermediate or near vision. The argument is that if this is provided in the center of the lens it will work well enough for the user in photopic conditions, because of large depth of field for tiny apertures, while this intensity provided for near and/or intermediate vision can be of use especially for mesopic conditions with slightly larger pupil sizes.
  • the addition of near and intermediate powers is important for mesopic conditions to enable viable vision for most ranges.
  • Eye model 1 uses a neutral cornea. Eye model 1 can be used to measure either the intensity or the Through Focus Modulation Transfer Function (MTF).
  • MTF Through Focus Modulation Transfer Function
  • Ip/mm measured line pairs per millimeter
  • a very advantageous way to construct a multifocal lens is to make use of a quadrifocal diffraction grating that provides far vision utilizing the -1 st order and provides near vision utilizing the near vision.
  • These quadrifocal gratings are formed so that on the main peak of each diffractive ring there is a have a shoulder, at about half the height of the main peak. This shoulder is on the central side of the peak it is attached to.
  • the shape of the diffractive unit cell has no discontinuities and the exact shape can be varied to achieve different intensity distributions.
  • Figure 1 shows, in a simplified manner, the anatomy of the human eye 10, for the purpose of illustrating the present disclosure.
  • the front part of the eye 10 is formed by the cornea 11, a spherical clear tissue that covers the pupil 12.
  • the pupil 12 is the adaptable light receiving part of the eye 10 that controls the amount of light received in the eye 10.
  • Light rays passing the pupil 12 are received at the natural crystalline lens 13, a small clear and flexible disk inside the eye 10, that focuses light rays onto the retina 14 at the rear part of the eye 10.
  • the retina 14 serves the image forming by the eye 10.
  • the posterior cavity 15, i.e. the space between the retina 14 and the lens 13, is filled with vitreous humour, a clear, jelly-like substance.
  • the anterior and posterior chambers 16, i.e. the space between the lens 13 and the cornea 11, is filled with aqueous humour, a clear, watery liquid.
  • Reference numeral 20 indicates the optical axis of the eye 10.
  • the lens 13 For a sharp and clear far field view by the eye 10, the lens 13 should be relatively flat, while for a sharp and clear near field view the lens 13 should be relatively curved.
  • the curvature of the lens 13 is controlled by the ciliary muscles (not shown) that are in turn controlled from the human brain.
  • a healthy eye 10 is able to accommodate, i.e. to control the lens 13, in a manner for providing a clear and sharp view of images at any distance in front of the cornea 11, between far field and near field.
  • Ophthalmic or artificial lenses are applied to correct vision by the eye 10 in combination with the lens 13, in which cases the ophthalmic lens is positioned in front of the cornea 11, or to replace the lens 13. In the latter case also indicated as aphakic ophthalmic lenses.
  • Multifocal ophthalmic lenses are used to enhance or correct vision by the eye 10 for various distances.
  • the ophthalmic lens is arranged for sharp and clear vision at three more or less discrete distances or focal points, often including far intermediate, and near vision, in Figure 1 indicated by reference numerals 17, 18 and 19, respectively.
  • Far vision is in optical terms when the incoming light rays are parallel or close to parallel.
  • the focal points 17, 18 and 19 may correspond to focal distances ranging from a few meters to tens of centimeters, to centimeters, respectively.
  • ophthalmologists choose lenses for the patients so that the far focus allows the patient to focus on parallel light, in the common optical terminology it is that the far is focused on infinity. Ophthalmologists will, when testing patients, commonly measure near vision as 40 cm distance from the eyes and intermediate vision at a distance of 66 cm, but other values can be used.
  • the amount of correction that an ophthalmic lens provides is called the optical power, OP, and is expressed in Diopter, D.
  • Figure 2 generally demonstrates a multifocal ophthalmic aphakic intraocular lens known in the art.
  • Diffractive lenses for ophthalmology applications make use of a combination of a diffractive grating and a refractive lens body.
  • Figure 2a shows a top view of a typical ophthalmic multifocal aphakic intraocular lens 30, and Figure 2b shows a side view of the lens 30.
  • the lens 30 comprises a light transmissive circular disk-shaped lens body 31 and a pair of haptics 32, that extend outwardly from the lens body 31, for supporting the lens 30 in the human eye. Note that this is one example of a haptic, and there are many known haptic designs.
  • the lens body 31 has a biconvex shape, comprising a center part 33, a front or anterior surface 34 and a rear or posterior surface 35.
  • the lens body 31 further comprises an optical axis 29 extending transverse to front and rear surfaces 34, 35 and through the center of the center part 33.
  • optical axis 29 is a virtual axis, for the purpose of referring the optical properties of the lens 30.
  • the convex lens body 31, in a practical embodiment, provides a refractive optical power of about 2D to 35D, with around 20D to 22D being the most common.
  • a periodic light transmissive diffraction grating or relief 36 is arranged, comprised of rings or zones extending concentrically with respect to the optical axis 29 through the center part 33 over at least part of the front surface 34 of the lens body 31.
  • the diffraction grating or relief 36 provides a set of diffractive focal points.
  • the diffraction grating or relief 36 may also be arranged at the rear surface 35 of the lens body 31, or at both surfaces 34, 35.
  • the diffraction grating 36 is not limited to concentric circular or annular ring-shaped zones, but includes concentric elliptic or oval shaped zones, for example, or more in general any type of concentric rotational zone shapes.
  • the optic diameter 37 of the lens body 31 is about 5 - 7 mm, while the total outer diameter 38 of the lens 30 including the haptics 31 is about 12- 14 mm.
  • the lens 30 may have a center thickness 39 of about 1 mm.
  • the haptics 32 at the lens body 31 are not provided, while the lens body 31 may have a plano-convex, a biconcave or plano-concave shape, or combinations of convex and concave shapes.
  • the lens body may comprise any of Hydrophobic Acrylic, Hydrophilic Acrylic, Silicone materials, or any other suitable light transmissive material for use in the human eye in case of an aphakic ophthalmic lens.
  • the lens body 31 may comprise a plano-convex, a biconcave or plano-concave shape, and combinations of convex and concave shapes or curvatures (not shown).
  • Figure 3a shows a top view of an ophthalmic multifocal aphakic intraocular lens 50, working in accordance with the present invention
  • Figure 3b shows a side view of the lens 50.
  • the difference over the prior art, exemplified in Figure 2a and 2b are in the optics of the lens.
  • the lens body 54 has a biconvex shape, comprising a front or anterior surface 52 and a rear or posterior surface 53.
  • the skilled person would know that for some embodiments one or both of the anterior surface 52 and the posterior surface 53 might be concave or planar, depending on the refractive baseline needed for a specific application.
  • the anterior surface 52 is formed as a summation of a Multifocal diffractive profile 51 and a refractive profile.
  • the refractive profile is often equal to the refractive baseline.
  • a refractive profile can be constructed as a summation of a refractive baseline and a corrective profile.
  • the refractive baseline is substantially monofocal and any substantially monofocal design can be used. It is of course well-known that any monofocal design takes into consideration both the anterior and posterior sides. The point being that any useful monofocal design can be used to define the refractive baselines of the current invention.
  • the multifocal diffractive profile operates over the advantageous and contiguous set of orders (-1, 0, +1, +2) arranged so that the -1 st order is arranged to provide far vision to a user and the +2 nd order is arranged to provide near vision.
  • the anterior surface 52 is drawn with a refractive baseline with larger radius, i.e. lower optical power, than typical, this is done purely for illustrative purposes, to keep the diffractive component visible.
  • the shape or height profile of the refractive baseline for any of the portions of the lens may be selected among a plurality of continuous refraction profiles known from monofocal lenses, such as spherical or any variant of aspherical profiles.
  • monofocal lenses such as spherical or any variant of aspherical profiles.
  • Most modern intraocular monofocal lenses are aspherical with the asphericity chosen to either be neutral and thus causing no further aberration in the eye, or they are purposefully induced to, given the optics of an average eye to exhibit negative spherical aberration to neutralize, fully or partly, the positive spherical aberration that is usually present in the human cornea.
  • Those choices should all be seen as different ways to create monofocal bases.
  • the invention disclosed hereby can be incorporated with any such monofocal base.
  • the manufacturing of refractive of diffractive surfaces can be carried out by any of laser micro machining, diamond turning, 3D printing, or any other machining or
  • Figures 4a, 4b, and 4c each show a lens profile for a lens made according to the present invention, shown here less the refractive baseline. These profiles are calculated, and later modelled for, a refractive index of 1.5359. All three diffractive profiles make use of diffractive unit cells with four main diffractive orders. The diffractive profiles are here shown from the center of the lens that coincides with the optical axis and out to the edge of optic surface at around a radius of 3 mm. The main difference, but not the only one, between the three profiles is different horizontal shift for each profile, defining the three of the main types of very useful quadrifocal lenses that can be manufactured.
  • Figures 4d, 4e, and 4f each show the modelled relative intensity distribution at different lens apertures of the lens profiles in Figures 4a, 4b, and 4c, respectively.
  • the lens profile in Figure 4a places a diffractive ring close to centered over the optical axis, a configuration that has four diffractive orders, -1, 0, +1, and +2, and as is shown by Figure 4d it is providing vision for a user at, respectively, around 19.0D, 20. ID, 21. ID, and 22.0D.
  • -1 st order corresponds to far vision
  • the near vision is addressed by the +2 nd order at an addition of 3D, which is above, but close to the lower limit of near addition for clinical interest.
  • the +l st order provides an addition of 2D, which is close to the ideal position of an intermediate addition.
  • the 0 th order is at ID addition over the far vision, which is well below intermediate vision, but it can certainly help to increase the total depth of focus.
  • the repeated diffractive unit cell in Figure 4a has a higher peak that is, in this case, 1.65pm peak-to-peak, where on each main peak there is a soft shoulder facing towards the center of the lens.
  • This configuration of the sinusoidal, or smooth, quadrifocal grating places a lowest intensity trough between the -1 st and the 0 th orders. This creates a configuration of very suitable ophthalmic lenses for users who want to be spectacle-free. This configuration provides a strong, but isolated, far vision and a rather continuous vision for near vision, intermediate vision and further.
  • the lens profile in Figure 4b places a trough of the diffractive ring close to centered over the optical axis, a configuration that has four diffractive orders, -1, 0, +1, and +2, and as is shown by Figure 4e it is providing vision for a user at, respectively, around 19.0D, 19.9, 21.0D, and 22.0D.
  • This lens functions similarly to the one described in Figures 4a and 4d, however, this configuration of the sinusoidal, or smooth quadrifocal grating places a lowest intensity trough between the 0 th and the+l st order. The lowest intensity point is not nearly as low as the one in Figure 4d. For 2 mm and 3 mm lens apertures this lens provides continuous vision mostly between far and near vision.
  • This version creates a configuration that is very suitable for ophthalmic lenses for users who want to be spectacle free.
  • This configuration provides a strong far vision that is broadened by the 0 th order. Intermediate and near vision are also provided, but the continuity of vision is less good than in the Intermediate-near configuration.
  • the unit cell for this lens changes significantly as a function of the lens aperture. This is done to provide the desired aperture-dependent tuning.
  • One very advantageous feature that was found out while exploring these diffractive profiles is that when tuning the grating to provide more intensity to the far vision (i.e., light corresponding to the lowest diffraction order) the grating became lower.
  • the +l st order is in this configuration severely suppressed because of the position at the center of the lens.
  • the lens functions similarly to the one described in Figures 4a and 4d and Figure 4b and 4e, however, this configuration of the sinusoidal, or smooth, quadrifocal grating has a lowest intensity point almost coinciding with the +l st order, rendering the almost a trifocal lens. It is even the case that the 2 nd order around 18D has a higher intensity than the +l st order.
  • This version creates a configuration that does provide good far and near vision and some intermediate vision, but there is no correctly placed order to provide strong intermediate vision.
  • Figure 5a shows a lens profile for a lens made according to the present invention, shown here less the refractive baseline. This profile is calculated, and later modelled for, a refractive index of 1.5359.
  • the diffractive profile is here shown from the center of the lens that coincides with the optical axis and out to the edge of optic surface at around a radius of 3 mm.
  • the profile in Figure 5a uses a quadrifocal unit cell that is tuned with increasing aperture to provide less near vision and more far vision. Additionally, it can be seen that the profile is bent downwards after a distance of 1.5 mm from the optical axis. This is due to positive spherical aberration being added to the profile for further tuning the lens performance. This added spherical aberration is corrective profile.
  • the profile in Figure 5a consists of the diffractive profile summed with a corrective profile. The full lens curvature is a summation of the refractive profile, the diffractive profile, and the corrective profile.
  • Figure 5b shows the modelled relative intensity distribution at different lens apertures of the lens profile in Figure 5a.
  • the lens has four diffractive orders, -1, 0, +1, and +2, and is providing vision for a user at, respectively, around 18.8D, 20. ID, 21.3D, and 22.4D.
  • -1 st order corresponds to far vision
  • the near vision is addressed by the +2 nd order at an addition of 3.6D, which is in the upper region of near additions.
  • the +l st order provides an addition of 2.5D, which is just above the desired range for intermediate addition.
  • the 0 th order gives 1.3D addition, which is somewhat below the lower bound of an intermediate addition.
  • This lens is similar in light distribution to the lens described in Figures 4a and 4d with a well-developed continuous vision between 0 th order to +2 nd order.
  • the relative light intensity decreases strongly for the +2 nd order and the +l st order.
  • the intensity of the 0 th order increases strongly with increasing aperture.
  • This intensity increases in the 0 th order is to some extent is caused by the tuning of the diffractive unit cell with increasing aperture, but it is also impacted by the positive spherical aberration that is added for apertures larger than 3 mm (1.5 mm radius).
  • This lens has four truly usable orders, each tuned in accordance with the lens aperture.
  • the intermediate focal point is here replaced by two different focal points, tuned so that the lower power focal point (0 th order) is dominant in photopic environments, while the higher power focal point is dominant in scotopic environments.
  • Figures 5c shows a lens profile for a lens made according to the present invention, shown here less the refractive baseline. This profile is calculated, and later modelled for, a refractive index of 1.5359.
  • the diffractive profile is here shown from the center of the lens that coincides with the optical axis and out to the edge of optic surface at around a radius of 3 mm.
  • the profile in Figure 5c uses a quadrifocal unit cell that is tuned with increasing aperture to provide less near vision and more far vision, specifically it is sharply tuned after the two first diffractive rings.
  • Figure 5d shows the modelled relative intensity distribution at different lens apertures of the lens profile in Figure 5c.
  • the lens has four diffractive orders, -1, 0, +1, and +2, and is providing vision for a user at, respectively, around 18.8D, 20.0D, 21. ID, and 22.4D.
  • -1 st order corresponds to far vision
  • the near vision is addressed by the +2 nd order at an addition of 3.6D, which is in the upper region of near additions.
  • the +l st order provides an addition of 2.3D, which is at the upper range for intermediate addition, but a good choice for intermediate addition.
  • the 0 th order gives 1.2D addition, which is below the lower bound of an intermediate addition.
  • This configuration has, for all apertures, a broadened far vision that merges together with the 0 th order for a more robust and wide far vision.
  • the relative light intensity decreases for the +2 nd order and the +l st order, and the intensity of the 0 th order becomes stronger than that of the +l st order.
  • the aim of this design is to provide light that is maximally physiologically usable, as the high additions cannot be used for large pupil sizes.
  • an ophthalmic multifocal lens arranged to provide far vision and at least one other usable vision, said lens having a light transmissive lens body with an optical axis and a refractive baseline that extends over at least a part of the lens body, and a diffraction grating configured to operate as an optical wave splitter, extending concentrically in radial direction, superpositioned onto at least one part of the refractive baseline is proposed.
  • said diffraction grating configured to operate as an optical wave splitter is further configured to be continuous at least within the central 3-millimeter aperture.
  • said far vision is provided by a -1 st diffractive order.
  • said near vision is provided by a +2 nd diffractive order.
  • At least two complete, consecutive periods of said diffraction grating comprise a pronounced shoulder, that is, a protrusion on the diffractive ring, said protrusion being on the central portion of the ring.
  • the intensity provided by the -1 st order is configured to be higher than the intensity provided by the +2 nd order for all lens apertures greater than 4 millimeters. According to yet another aspect of the present disclosure, the intensity provided by -1 st order is configured to be greater than that of the 0 th and +l st orders, respectively, for lens apertures between 3 millimeters and 4 millimeters.
  • said +l st order is configured to provide a stronger light intensity than that of the 0 th order at a lens aperture of 3 millimeters, whereas the 0 th order is configured to provide a stronger light intensity than that of the +l st order for lens apertures larger than 5 millimeters.
  • either one of the +l st or 0 th orders is suppressed to have less 10% of light intensity when measured according to ISO 11979-2 with Eye Model 1
  • a corrective profile is added to the diffractive profile to increase one of the orders -1 st , 0 th , +l st or +2 nd .

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  • Health & Medical Sciences (AREA)
  • Ophthalmology & Optometry (AREA)
  • Physics & Mathematics (AREA)
  • General Health & Medical Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • Optics & Photonics (AREA)
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Abstract

L'invention concerne une lentille ophtalmique multifocale, conçue pour fournir une vision de loin et au moins une autre vision utilisable. Ladite lentille a un corps de lentille transmettant la lumière avec un axe optique et une ligne de base de réfraction qui s'étend sur au moins une partie du corps de lentille, et un réseau de diffraction configuré pour fonctionner en tant que diviseur d'onde optique, s'étendant de manière concentrique dans la direction radiale, superposé sur au moins une partie de la ligne de base de réfraction. Ledit réseau de diffraction est configuré pour fonctionner en tant que diviseur d'onde optique est en outre configuré pour être continu au moins à l'intérieur de l'ouverture centrale de 3 millimètres, tandis que ladite vision de loin est fournie par un -1ierordre de diffraction, et ; ladite vision de près est fournie par un +2ième ordre de diffraction.
EP22917631.8A 2022-12-30 2022-12-30 Lentille oculaire diffractive quadrifocale Pending EP4655640A1 (fr)

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Family Cites Families (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5344447A (en) 1992-11-12 1994-09-06 Massachusetts Institute Of Technology Diffractive trifocal intra-ocular lens design
US5760871A (en) 1993-01-06 1998-06-02 Holo-Or Ltd. Diffractive multi-focal lens
US10426599B2 (en) 2016-11-29 2019-10-01 Novartis Ag Multifocal lens having reduced chromatic aberrations
HUE050405T2 (hu) * 2017-07-26 2020-12-28 Vsy Biyoteknoloji Ve Ilac Sanayi Anonim Sirketi Multifokális szemészeti diffrakciós lencse
EP3849470A4 (fr) 2018-09-13 2022-06-01 Hanita Lenses R.C.A. Lentille intraoculaire multifocale
MX2021007513A (es) * 2018-12-20 2021-08-11 Aaren Scientific Inc Lente intraocular difractiva pentafocal.
AU2019472967A1 (en) * 2019-11-08 2022-05-19 Vsy Biyoteknoloji Ve Ilaç San. A.S. A new generation ophthalmic multifocal lenses
EP4157146A1 (fr) 2020-06-01 2023-04-05 Icares Medicus, Inc. Lentille multifocale diffractive asphérique double face, fabrication et utilisations de cette dernière
AU2021428508B2 (en) 2021-02-19 2025-09-18 Vsy Biyoteknoloji Ve Ilac Sanayi A.S. An adaptive multifocal diffractive ocular lens

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