Lens with extended depth of focus by inducing excessive longitudinal chromatic aberration

Abstract

In particular, an implantable lens is disclosed that includes refractive elements that cause chromatic aberration and elements that cause an increase in chromatic aberration. A method for producing an implantable lens is also disclosed.

Description

Technical Field

[0001] The following disclosure relates to the field of implantable lenses, such as intraocular lenses (IOLs) or phakic lenses, and in particular to implantable lenses that induce excess longitudinal chromatic aberration (LCA) to extend the depth of focus (DoF) of the eye, such as after removal of the natural crystalline lens. Background Art

[0002] Treatment of eye disorders may include, for example, removal of the natural lens during cataract surgery. In these cases, the lost optical power is typically replaced by an intraocular lens that can be implanted in the position of the previous natural lens. Other cases of treating eye diseases may involve keeping the natural lens intact, but correcting high refractive errors, for example, by using a phakic lens. Typically, a monofocal intraocular lens can be used for eye disorder treatment, which converges light approximately to a focus, which determines the point at which the patient can see clearly. However, objects located before or after the focal plane are blurred and therefore cannot be identified by the patient. Alternatively, a multifocal lens, such as a bifocal or trifocal lens, is used, such as described in US2014 / 0168602A1, which extends the depth of focus by introducing more than one focal plane. For example, these focal planes divide the incident light into a primary focus and a secondary focus, resulting in reduced visual quality due to energy distribution. In addition, a lens with a standard partition design may exhibit dependence on the pupil of an individual patient. Typically, monofocal or multifocal lenses are configured to provide reduced chromatic aberration, as chromatic aberration is generally considered to be a detrimental effect on the imaging quality of the lens.

[0003] Patent application US2019 / 0110889A1 considers combining a refractive structure and a diffractive structure to produce a multichromatic lens, wherein the refractive structure has positive refractive power.

[0004] European Patent 83305354.9 discloses an ophthalmic lens having refractive power and diffractive power, wherein the diffractive power is provided by a transmission / surface relief hologram.

[0005] US 2010 / 0312337 A1 and US 2014 / 0168602 A1 propose ophthalmic lenses that apply diffractive profiles to reduce LCA. Summary of the invention

[0006] Therefore, the object of the present invention is to propose an implantable lens that overcomes the disadvantages of known lenses, and in particular to propose an implantable lens (e.g. an intraocular lens) that provides an extended depth of focus, which meets the needs of pseudophakic patients, for example after cataract surgery, in particular with regard to enhancing the patient's range of vision with minimal side effects.

[0007] According to a first exemplary aspect, the object is solved by an implantable lens comprising a refractive element causing chromatic aberration and an element causing an increase in chromatic aberration, wherein the element causing an increase in chromatic aberration comprises a diffractive structure, wherein the diffractive structure is a negative diffractive structure, and wherein the diffractive structure is a Kinoform lens structure. Thus, the diffractive structure may be a negative or divergent Kinoform lens structure, such that it may exhibit or produce a negative focal length and may diverge incident light rays. Thus, as a Kinoform structure acting as a negative lens, it may increase the LCA. The negative or divergent Kinoform lens structure may reduce the base power of the refractive component, in particular between -3D and -8D, such as -3.75D or -7.25D.

[0008] As an example, an implantable lens is disclosed, comprising a refractive element causing chromatic aberration and an element causing an increase in chromatic aberration, wherein the element causing an increase in chromatic aberration comprises a diffractive structure to diverge incident light rays having a negative focal length, wherein the diffractive structure is a Kinoform lens structure. As another example, an implantable lens is disclosed, comprising a refractive element causing chromatic aberration and a diffractive element causing an increase in chromatic aberration (of the refractive element), wherein the diffractive element causing an increase in chromatic aberration comprises a negative diffractive structure, and wherein the diffractive structure is a Kinoform lens structure.

[0009] The implantable lens can be, for example, an ophthalmic lens, an intraocular lens (IOL), a pseudophakia or an auxiliary lens. An implantable lens can be understood as an intraocular lens (IOL) for implantation (e.g., in the capsular bag), or an auxiliary sulcus fixed lens or a phakic lens. The implantable lens and / or the refractive element can have a size (e.g., diameter) of 5.5 mm to 7 mm (e.g., 6 mm).

[0010] The phakic lens may be a phakic intraocular lens, which may be understood as an artificial lens surgically implanted in the eye to correct myopia (ie, nearsightedness). A phakic lens may be used where the natural lens remains intact in the eye.

[0011] An artificial lens is understood to be a lens that is implanted in the eye, for example as part of a cataract or myopia treatment. Such an IOL may be implanted, for example during cataract surgery, after the natural lens of the eye, which has, for example, a cataract, has been removed. The purpose of a pseudophakic IOL is to simulate the same light-gathering function as a natural lens.

[0012] Phakic intraocular lenses can be placed in the anterior chamber to work with the existing natural lens and can be used, for example, in refractive surgery to change the optical power (optical power) of the eye, for example in the treatment of myopia. An auxiliary lens can be understood as a lens that is implanted in the eye (e.g., in the sulcus) together with another lens (e.g., a standard intracapsular lens). In addition, the auxiliary lens can have a different geometry than the IOL. For example, the refractive element of the IOL can be biconvex, i.e., both the rear surface and the front surface are convex. However, the refractive element of the auxiliary lens can have one convex surface and another concave surface, for example the refractive element can have a converging meniscus or a negative or positive meniscus.

[0013] An implantable lens or IOL according to a first aspect may include or be composed of a small (e.g., plastic) lens having (e.g., plastic) side pillars (e.g., haptics) to hold the lens in place in a capsular bag within the eye. The haptics may have a circular or spiral form, which may allow for precise centering and fixation within the eye. The IOL may be placed, for example, in the anterior chamber or posterior chamber or in the capsular bag during cataract surgery. For example, during surgery, a cataractous lens may be removed from its capsular bag and replaced with an implantable lens according to the first exemplary aspect. An implantable lens according to the first exemplary aspect may include or be composed of (or made of) a foldable material (i.e., a material that can be folded), which may enable insertion into an incision up to 4 mm in diameter and may minimize any damage that may be caused by surgery and postoperative scarring. For example, the implantable lens according to the first exemplary aspect may include or be composed of (or made of) a plastic, such as polymethyl methacrylate (PMMA), hydrophobic acrylics (e.g., phenethyl methacrylate (PEMA) and phenethyl acrylate (PEA)); hydrophilic acrylics (e.g., polyhydroxyethyl methacrylate (pHEMA)); and / or silicones (e.g., polydimethylsiloxane (PDMS)), which may prevent postoperative complications associated with scarring.

[0014] The groove may be a ciliary groove, which may be understood as a small space between the rear surface of the iris base and the front surface of the ciliary body. According to a first exemplary aspect, the groove may be used to fix the implantable lens, which may provide good long-term stability and safety.

[0015] The capsular bag may be understood as the sac-like structure that remains in the eye after extracapsular cataract extraction or phacoemulsification. An implant (intraocular) lens may be placed in this structure to recreate the (original) phakic eye state.

[0016] A refractive element causing chromatic aberration may be an optical element that causes refraction and exhibits (longitudinal) chromatic aberration (LCA). Chromatic aberration may be caused by dispersion within the refractive element, for example the refractive index of the lens element may vary with the wavelength of the incident light. Since the focal length of the lens may depend on the refractive index, changes in the refractive index may affect the focusing. The refractive element causing chromatic aberration may be a lens, for example a biconcave lens. It may be a monofocal or multifocal implantable lens, for example an extended depth of focus, a bifocal or a trifocal lens. The refractive element may have a basic (i.e., intrinsic) LCA of up to (approximately) 1D, or may have a basic LCA of less than 0.25D. The LCA may be determined as the nominal focal power of the refractive element (e.g. of the lens) measured at the two extreme ends of the spectrum (e.g. 450nm and 650nm), for example:

[0017] LCA=P(λ2)-P(λ1)

[0018] Where λ1 and λ2 may be different wavelengths of light (e.g. 450 nm and 650 nm), for a diffractive element, the LCA may depend on the design wavelength λ0 (e.g. 550 nm) and the (refractive) power P0 of the diffractive element at wavelength λ0. The LCA may be measured, for example, by measuring P(λ1), P(λ2), or estimated based on the wavelength. The focal power in diopters (D) may be the reciprocal of the focal length of the dioptric element (e.g. a lens) measured in a specific medium with a given refractive index (e.g. a medium with n=1.336, such as aqueous humor when measured in vivo, in particular in situ, e.g. in the eye, or a balanced salt solution when measured in vitro, in particular in an immersion fluid). The (longitudinal) chromatic aberration may depend on the Abbe number of the material used. The Abbe number or V number of a (transparent) material is an approximate measure of the material dispersion (i.e. the variation of the refractive index with the wavelength of the incident light), and a high value of V may indicate a low dispersion. The (IOL) refractive element may have an Abbe number of 30 to 60, in particular 40 to 50, such as 42 or 46, for example, the refractive element may be made of a material having an Abbe number of 30 to 60, in particular 40 to 50, such as 36, 42, 46 or 55. The refractive element may have a basic (refractive) power or a nominal focal range of 0D to 40D, in particular 10D to 30D, such as 20D to 30D. The refractive element causing chromatic aberration may have a central thickness of up to 2 mm, such as 1 mm, wherein the central thickness may be the thickness of the refractive element along its optical axis, such as the thickness of the refractive element along an axis about which the refractive element may be rotationally symmetric, such as in the case where the refractive element is a lens. The refractive index of the refractive element may be greater than 1, preferably at least 1.01 or at least 1.3 and / or at most 3, more preferably at least 1.4 and / or at most 2, in particular (about) 1.5, such as 1.49 or 1.52; for example, the refractive element may be made of a material having a refractive index greater than 1, preferably at least 1.01 and / or at most 3, more preferably at least 1.3 and / or at most 2, in particular (about) 1.5, such as 1.49 or 1.52. The refractive element may have a refractive index higher than the median refractive index of the eye, for example higher than 1.336. The refractive index is relative to a light wavelength of 589 nm. The refractive element causing chromatic aberration may be made of an optical material (e.g. a biological material), for example an amorphous or single-crystalline material, such as PMMA, silicone, acrylate. For example, the refractive element may include or be made of, for example, polymethyl methacrylate (PMMA), hydrophobic acrylics (e.g., phenethyl methacrylate (PEMA) and phenethyl acrylate (PEA)); hydrophilic acrylics (e.g., polyhydroxyethyl methacrylate (pHEMA)); and / or silicones (e.g., polydimethylsiloxane (PDMS)). The refractive element may present a convex surface (structure), which may be, for example, biconvex, such as a biconvex lens.In particular, the refractive element can induce chromatic aberration, wherein the distance between the focal points of red and blue light is 1 mm to 2 mm when measured in immersion fluid (eg, as described above), and / or 0.4 mm to 0.6 mm when measured in situ or in the eye.

[0019] An element causing an increase (or excess, excess or excess amount) of chromatic aberration may be an element that increases chromatic aberration relative to, for example, the (intrinsic) chromatic aberration of a refractive element (e.g., the chromatic aberration exhibited by the refractive element). The chromatic aberration may be a longitudinal chromatic aberration (LCA). For example, an element causing an increase in chromatic aberration may be an element that increases longitudinal chromatic aberration. The (longitudinal) chromatic aberration may increase, for example, by 1D, 2D, 3D, 3.5D or more to about 4D, in particular for light wavelengths of 450nm to 650nm. For example, the LCA may depend on the material and the (optical) power of the implantable lens and / or the refractive element and / or the element causing the increase in chromatic aberration. The increase in LCA may be an increase by a certain value (e.g., from a basic power of 0.25D to 3D or 4D). For example, the element causing the increase in chromatic aberration may increase the distance between the focal points of different wavelengths of light, for example by further separating the focal points of different wavelengths of light, it may for example increase the distance between the focal points (e.g. focal planes) of red light (e.g. wavelength of 650 nm) and blue light (e.g. wavelength of 450 nm), for example depending on the lens power of the refractive element and its Abbe number. For example, under standard room conditions (e.g. temperature of 20° C. (293.15 K), absolute pressure of 1 atm (101.325 kPa), dry air atmosphere), the distance between the focal points of red light and blue light may increase to at least 5 mm or 6 mm or at least 9 mm, the distance may increase to, for example, 6 mm to 12 mm or 13 mm, for example about 6.8 mm or 11.4 mm. Preferably, the distance between the focal points of red light (e.g. 656 nm) and blue light (e.g. 486 nm) may be between 5 mm and 10 mm when measured in immersion fluid, wherein the immersion fluid has a refractive index of 1.333 (i.e. the refractive index of the surrounding medium of the lens during measurement), and / or the distance between the focal points of red light (e.g. 656 nm) and blue light (e.g. 486 nm) may be between 0.8 mm and 1.3 mm when measured in situ (e.g. in the eye). Thus, the chromatic focus shift between 656 nm and 486 nm may be between 5 mm and 10 mm when in immersion fluid and between 0.8 mm and 1.3 mm when in situ. For comparison, the chromatic shift of the refractive element between 656 nm and 486 nm may be about 1 mm to 2 mm (when in immersion fluid) and / or about 0.5 mm in situ. For example, the refractive element may cause chromatic aberration, wherein the distance between the focal points of red and blue light is 1 mm to 2 mm when measured in immersion fluid, and / or 0.4 mm to 0.6 mm when measured in situ. The element causing an increase in chromatic aberration may include or be composed of (e.g., be made of) any suitable material (e.g., a biological material), such as any material described in the context of a refractive element causing chromatic aberration, such as the same material or a biological material as the refractive element causing chromatic aberration.For example, the refractive element that causes chromatic aberration and the element that causes increased chromatic aberration may include or be composed of (e.g., made of) the same material or different materials. The element that causes increased chromatic aberration may be attached to, placed on, or formed on the rear surface or the front surface of the refractive element. The element that causes increased chromatic aberration may have a back surface that is consistent with the rear surface or the front surface of the refractive element, or the element that causes increased chromatic aberration may be smaller, such as limited to the central lens area, such as 3mm to 4mm in diameter. The smaller element that causes increased chromatic aberration may further allow for improved vision in medium light and dark light.

[0020] In contrast to standard approaches to minimizing chromatic aberration, it has surprisingly been found that increasing chromatic aberration using an element that causes an increase in chromatic aberration can be beneficial, for example, in extending the depth of focus relative to a monofocal lens, such as for treating pseudophakic patients or for treating presbyopia without removing the natural lens. For example, the increase in chromatic aberration can provide an extended focus shift, which can result in extending the patient's visual range in polychromatic light. Thus, an implantable lens according to the first exemplary aspect can extend the focus by incorporating various wavelengths of light from the visible range to enable better vision at different distances in a patient after cataract surgery.

[0021] The implantable lens according to the first exemplary aspect may also be completely independent of the pupil, which is not feasible, for example, in a refractive enhancement monofocal lens, which may use the central portion of the lens to induce defocus. The implantable lens according to the first exemplary aspect may also be more tolerant to post-operative refractive surprises due to the stretching of the multi-color focus. Thus, the implantable lens according to the first exemplary aspect may enhance the patient's visual range while minimizing the side effects associated with standard methods of spectroscopic treatment. In addition, the implantable lens according to the first exemplary aspect may be more cost-effective, for example more cost-effective to produce than, for example, a multifocal lens, for example because more cost-effective materials, for example, having a lower Abbe number, may be used.

[0022] According to a first exemplary embodiment of the implantable lens of the first exemplary aspect, the increase in chromatic aberration is an increase of at least two times, preferably at least three times, in particular between three times and seven times (e.g. in situ or in immersion liquid). It has been found that in order to enhance the effect achieved, a higher increase in chromatic aberration may be preferred. However, using cost-effective materials, an increase of more than 7 times may not be feasible. This multiple may be a multiple compared to the chromatic aberration caused by the refractive element (e.g. caused only by the dispersion of the refractive element), for example, caused by the refractive lens base which can be measured in immersion liquid.

[0023] According to a second exemplary embodiment of the implantable lens of the first exemplary aspect, the refractive element has a rear surface and a front surface, and the rear surface and / or the front surface has an aspherical shape or a spherical shape. The aspherical shape or the spherical shape can enhance the optical properties of the refractive element, and can allow precise adaptation of the refraction of the refractive element, and can further enhance the patient's visual range while minimizing side effects. A spherical shape (e.g., a surface profile of the refractive element (e.g., a lens) is a portion of a sphere) or a cylindrical shape (e.g., a surface profile of the refractive element (e.g., a lens) is a portion of a cylinder) may be easier and more cost-effective to produce. An aspherical shape (i.e., a non-spherical shape, e.g., a lens whose surface profile is not a portion of a sphere or a cylinder) can avoid, reduce or eliminate spherical aberrations, and thus further enhance the patient's visual range while minimizing side effects.

[0024] The Abbe number of the element causing increased chromatic aberration can be 30 to 60, in particular 40 to 50, for example 42 or 46. For example, the element causing increased chromatic aberration can be made of a material having an Abbe number of 30 to 60, in particular 40 to 50, for example 36, 42, 46 or 55.

[0025] When the lens is implanted, the posterior surface and the anterior surface can be defined by the direction of incident light propagating from the outside into the eye, so that the posterior surface is the surface through which the incident light first passes, i.e., the surface facing the outside or the cornea when the lens is implanted, and the anterior surface faces the interior of the eye, such as the vitreoretinal cavity or the retina, when the lens is implanted.

[0026] According to a third exemplary embodiment of the implantable lens of the first exemplary aspect, the element causing the increase in chromatic aberration comprises a diffractive structure, in particular the diffractive structure is a Fresnel structure, in particular a Kinoform lens structure.

[0027] The diffractive structure may be an optical structure, for example, specifically designed to cause diffraction of incident light. The diffractive structure may utilize a first diffraction order and a second diffraction order, and / or (for example partially) a third diffraction order. The first diffraction order and / or the second diffraction order may be positive or negative, i.e. have a positive or negative sign, respectively. Preferred examples of diffractive structures may be Fresnel structures or more preferably Kinoform lens structures, which may allow for more cost-effective manufacturing and enhanced adaptability to patient needs. The diffractive structure may allow for further enhanced increases in chromatic aberrations, and further enhance the patient's visual range while minimizing side effects. The Kinoform lens structure may further provide enhanced focusing efficiency, for example, a Kinoform made of a non-absorptive but refractive material may have a focusing efficiency of 100%, further enhancing the patient's visual range while minimizing side effects. The diffractive structure may be attached to, placed on or formed on the rear or front surface of the refractive element. The diffractive structure may have a back surface that coincides with the back or front surface of the dioptric element, or the diffractive structure may be smaller, such as limited to the central lens area, such as 3mm to 4mm in diameter. Smaller diffractive structures may further allow for improved mesoscopic and scotopic vision.

[0028] The Fresnel structure may be or include a Kinoform lens structure. A Kinoform lens may be a diffractive / refractive optical device utilizing two modes, which may ensure maximum efficiency. A Kinoform lens structure may have a (generally) parabolic surface profile (e.g., a surface undulation profile). A Kinoform lens structure may have a waveband (e.g., extending from a minimum height in the structure to a maximum height) and a step height (i.e., the maximum height difference within the waveband). The wavebands in a Kinoform lens structure may be in the form of a torus ring; however, these wavebands may take other shapes, such as strips (as in conventional spectral gratings) and ellipses (to produce different focal lengths at different angular orientations around the optical axis). In addition, a group of wavebands may be arranged in a two-dimensional array of cells, with each cell acting as a separate optical element. Within each waveband, the theoretically optimal depth profile may be a smooth curve extending continuously from the highest region to the lowest region; however, for ease of manufacturing, the optimal profile may be approximated as a series of steps (phase levels), each step having a constant depth. The surface relief profile t(r) can be approximately determined from the relationship: t(r) = [λ / 2π(μ-1)][Φ(r)]2π, where λ is the wavelength of light, μ is the refractive index of the optical material (of the surface relief profile), and [Φ(r)]2π is the phase function Φ(r) modulo 2π. Kinoform lens structures can present arbitrary phase distributions, such as interference patterns defined by two arbitrary coherent point sources on an arbitrary surface, to which any 2-dimensional phase distribution defined by an arbitrary polynomial can be added. In particular, a Kinoform lens structure can be described by an interference pattern generated on a plane perpendicular to the optical axis defined by two points, one of which is at infinity. A Kinoform lens structure can be manufactured by etching or machining ridges in a surface, such as the (posterior and / or anterior) surface of a refractive element, for example by stepwise approximation or gray-scale direct milling IBL. The Kinoform lens structure can be made of optical materials, for example, amorphous or single-crystalline materials such as PMMA, silicone, acrylates. For example, the Kinoform lens structure can include or be made of plastics, such as polymethyl methacrylate (PMMA), hydrophobic acrylics (e.g., phenethyl methacrylate (PEMA) and phenethyl acrylate (PEA)); hydrophilic acrylics (e.g., polyhydroxyethyl methacrylate (pHEMA)); and / or silicones (e.g., polydimethylsiloxane (PDMS)).

[0029] The Kinoform lens structure may consist of or may comprise a continuous "sawtooth" surface profile, which may cause light divergence, as described in further detail below by way of example. In particular, the (negative) Kinoform lens structure may exhibit a diffraction (surface) profile having a local minimum in the center (which may be at least partially superimposed on the surface of the diopter element), thus for example without a central protrusion pointing outwards (relative to the diopter element, e.g. along the optical axis), and the distance between the "sawtooth" maxima may decrease with distance from the center. For example, the Kinoform lens structure may have a central zone that is lower relative to the first diffraction step (the first one relative to the center).

[0030] The Kinoform lens structure may be or include a Fresnel phase zone plate structure. The Fresnel phase zone plate structure may be similar in appearance to the Fresnel lens structure. The Fresnel phase zone plate structure may include several concentric rings (corresponding to each band) having a band radius. From the side, the Fresnel phase zone plate structure may look like a series of sawtooth ridges. The Fresnel phase zone plate structure may be based on diffraction rather than refraction (diopter), and may have more bands (e.g., 10 to 40 or 15 to 30) and a much smaller height difference (i.e., step height) between adjacent bands than a Fresnel lens. The step height within a band may, for example, correspond to a phase change of 2π (one wavelength). The step height may, for example, be at least 0.1 μm, at least 0.6 μm, or at least 1 μm and / or at most 10 μm, for example, the step height may be 6.7 μm. The Fresnel phase zone plate structure may, for example, comprise 10 to 40 or 15 to 30 zones (e.g. in the form of concentric rings around the optical axis of the diopter). The minimum zone radius may be at least 0.4 mm, in particular at least 0.55 mm or at least 0.76 mm, and / or at most 1 mm. For example, the LCA may depend on the material and (optical) power of the implantable lens and / or the diopter and / or the element causing the increase in chromatic aberration. The increase in LCA may be an increase by a certain value (e.g. from a basic power of 0.25 D to 3D or 4D). For implantable lenses with diopter elements having a basic power between zero and 40 D, a unique Kinoform (lens) structure may be designed. For example, the Kinoform lens structure may be formed on or in the rear and / or front surface of the diopter. The Kinoform lens structure may extend from the center of the refractive element to its edge, e.g. from the center of the posterior or anterior surface to the edge of the posterior or anterior surface, respectively. Alternatively, the Kinoform lens structure may extend from the center of the refractive element to a distance smaller than the distance between the center of the refractive element and its edge, e.g. from the center of the posterior or anterior surface to a distance smaller than the maximum (radial) distance from the center of the posterior or anterior surface to the edge of the (respective) posterior or anterior surface, e.g. a (radial) distance of 1.5 mm to 2 mm (e.g. 2.25 mm) (measured from the center). Thus, the Kinoform lens structure may, e.g., be confined to a central region of the surface of the refractive element, e.g. of 3 mm to 4 mm / 4.5 mm in diameter, which may further allow for improved mesoscopic and scotopic vision.

[0031] According to another exemplary embodiment of the implantable lens of the first exemplary aspect, the refractive element has a rear surface and a front surface, and the diffractive structure is on the rear surface and / or the front surface. In this way, the diffractive structure can be advantageously placed and / or distributed on the surface of the refractive element, and thus the patient's visual range can be further enhanced while minimizing side effects.

[0032] According to another exemplary embodiment of the implantable lens of the first exemplary aspect, the diffractive structure is a negative diffractive structure, in particular having a focal power of at most -1D, preferably a focal power between -1D and -11D (i.e., at least -11D and / or at most -1D), and more preferably at least -8D and / or at most -3D, such as -7D. Negative diffractive structures, in particular negative diffractive structures having a focal power of at most -1D, can further enhance the patient's visual range while minimizing side effects. However, a focal power of less than -11D may not be cost-effective to manufacture and may produce additional side effects.

[0033] According to another exemplary embodiment of the implantable lens of the first exemplary aspect, the diffractive structure comprises a diffractive profile, and in particular, the diffractive profile extends from a first Fresnel zone of the diffractive structure to an edge of the diopter element, or the diffractive profile extends from a center of the diopter element to an edge of the diopter element. The diffractive profile may be a profile that causes diffraction of light. The diffractive profile may be a profile formed (e.g., etched or laser formed) into the rear surface and / or the front surface. The first Fresnel zone may be centered, for example, at the center of the rear surface or the front surface, for example, the axis about which the first Fresnel zone is rotationally symmetric may be the optical axis of the diopter element. The edge may be, for example, an edge of the front surface or the rear surface. Using a diffractive profile, such as a Kinoform profile (i.e., a diffractive profile having a Kinoform lens structure) further enhances the patient's visual range while minimizing side effects.

[0034] The diffraction profile may be a continuous "sawtooth" surface profile which may have a local minimum in the center, so that for example there is no central bulge pointing outwards, and the distance between the "sawtooth" maxima may decrease away from the center.

[0035] According to another exemplary embodiment of the implantable lens of the first exemplary aspect, the refractive element and the element causing the increase in chromatic aberration together include or form a diffraction-refractive zone (approximately) centered at the center of the refractive element, in particular, the diffraction-refractive zone has a diameter from 3 mm to 4.5 mm (and, for example, the surface of the refractive element can have a diameter of 5.5 mm to 7 mm, on which the diffraction-refractive zone is formed). The diffraction-refractive zone can be formed, for example, by a diffraction profile and, for example, a refractive element (for example, a surface having a concave or convex form) together, and by a diffraction profile formed (for example, etched) into the surface of the refractive element. The diffraction-refractive zone can be formed, for example, by a Kinoform profile. The center of the refractive element can be defined by the optical axis of the implantable lens. The optical axis can be an axis about which the implantable lens and / or the refractive element present (approximately) rotational symmetry. The optical axis can, for example, pass through the center of curvature of each surface of the implantable lens and / or the refractive element, and can coincide with the axis of rotational symmetry. The optical axis may for example coincide with the mechanical axis of the implantable lens and / or the refractive element.The diffractive-refractive zone may allow further enhancement of the patient's visual range while minimizing side effects.

[0036] The portion of the surface of the refractive element that is not covered by the diffractive-refractive zone (e.g., the outer zone) can be only refractive without causing diffraction effects. The outer zone can be a ring with an inner diameter of 3mm to 4.5mm and an outer diameter of 5.5mm to 7mm, or extending to the edge of the corresponding surface of the refractive element. The outer zone can allow for refractive power compensation and can further enhance the patient's visual range while minimizing side effects.

[0037] According to another exemplary embodiment of the implantable lens of the first exemplary aspect, the diffractive structure utilizes a first and / or second (e.g., positive or negative) diffraction order. For example, in the case where the implantable lens and / or the refractive element is or includes a bifocal or trifocal lens (e.g., where the first order and the second order are used simultaneously), the simultaneous action of both the first order and the second order can be utilized. This can allow for further enhancement of the patient's visual range while minimizing side effects.

[0038] According to another exemplary embodiment of the implantable lens of the first exemplary aspect, the diffractive element and the element causing the chromatic aberration increase direct light about a specific wavelength (e.g., a wavelength of 550nm, 555nm, or 546nm) to the same focus. This can allow further enhancement of the patient's visual range while minimizing side effects.

[0039] According to another exemplary embodiment of the implantable lens of the first exemplary aspect, the implantable lens has a monochromatic modulation transfer function (MTF) of 0.43 or better (e.g., higher) at 100 lp / mm, preferably has a monochromatic modulation transfer function (MTF) of 0.5 or better (e.g., higher) at 100 lp / mm, more preferably 0.6 or better. The implantable lens may meet the optical quality standards of monofocal lenses, such as those defined in standard ISO11979-2:2014. Such an implantable lens may allow for enhanced optical performance. This may allow for further enhancement of the patient's visual range while minimizing side effects.

[0040] According to another exemplary embodiment of the implantable lens of the first exemplary aspect, the refractive element has a nominal focal power range of -5D to 40D or 0D to 40D, in particular 20D to 30D. This may allow further enhancing the patient's visual range while minimizing side effects.

[0041] According to another exemplary embodiment of the implantable lens of the first exemplary aspect, the element causing an increase in chromatic aberration increases the chromatic aberration by at least 1D, preferably at least 2D, in the spectral range of 450nm to 650nm. For example, the element causing an increase in chromatic aberration may increase the chromatic aberration of a pseudophakic eye by at least 1D, preferably at least 2D, in the spectral range of 450nm to 650nm. This may allow further enhancement of the patient's visual range while avoiding or minimizing side effects.

[0042] According to another exemplary embodiment of the implantable lens of the first exemplary aspect, the element causing the increase in chromatic aberration and the refractive element are composed of the same material, in particular, the element causing the increase in chromatic aberration and the refractive element form an integral unit, for example, by forming the element causing the increase in chromatic aberration on or in the refractive element. This can allow the patient's visual range to be further enhanced while minimizing side effects.

[0043] According to another exemplary embodiment of the implantable lens of the first exemplary aspect, the Kinoform lens structure comprises a sawtooth surface profile, which is particularly superimposed on the front surface and / or the back surface of the refractive element, wherein optionally the Kinoform lens structure can have a central zone that is lower relative to the first diffraction step.

[0044] According to another example of the implantable lens of the first exemplary aspect, the sawtooth surface profile presents a local minimum at the center (i.e., at radius 0), and in particular the distance between the maximum values ​​at which the sawtooth surface profile reaches the step height decreases as the distance away from the center decreases. For example, when the sawtooth surface profile is centered on the center of the refractive element, the center may correspond to the center of the refractive element. In order to account for any irregularities caused by the surface structure of the refractive element (e.g., convex surface), the maximum and minimum values ​​may be determined relative to a baseline, which corresponds to the corresponding surface of the refractive element.

[0045] According to a second exemplary aspect, the above object is solved by a method for producing an implantable lens according to the first exemplary aspect, the method comprising etching and / or machining an element causing an increase in chromatic aberration on the front surface and / or the back surface of the refractive element.

[0046] Another exemplary embodiment of the implantable lens according to the first exemplary aspect can be a refractive-diffractive hybrid intraocular lens. For example, the implantable lens can have a rear surface and a front surface, wherein one or both surfaces are, for example, aspherical or have, for example, a spherical shape, and one or both surfaces have, for example, a Fresnel or Kinoform lens structure, which produces a negative (divergent) lens refractive effect, for example to compensate for the excess of the positive refractive power of the basic refractive element, while both the diffractive and refractive structures contribute to monofocality. The implantable lens can include a refractive element with refractive dispersion and a Fresnel or Kinoform lens structure with diffractive dispersion, or be composed of a refractive element with refractive dispersion and a Fresnel or Kinoform lens structure with diffractive dispersion. The (Fresnel) lens power of the Fresnel or Kinoform lens structure, for example, ranges from -1D to -11D. The (hybrid) refractive-diffractive intraocular lens can have a nominal power range of about 0D to about 40D. The implantable lens can be designed to increase the chromatic aberration of pseudophakic eyes by about 1D in the spectral range of 450nm to 650nm, for example by combining refractive and diffractive chromatic aberrations. The intraocular lens according to claim 2 increases the chromatic aberration of pseudophakic eyes by about 2D in the spectral range of 450nm to 650nm by combining refractive and diffractive chromatic aberrations. The implantable lens (e.g., a refractive-diffractive intraocular lens) can, for example, utilize a first (e.g., positive or negative) diffractive order of a negative diffractive element and / or a second (e.g., positive or negative) diffractive order of a negative diffractive element. The implantable lens (e.g., a refractive-diffractive intraocular lens) can have a diffraction profile spanning from a first Fresnel wave zone to the edge of the lens. The implantable lens (e.g., a refractive-diffractive intraocular lens) can have a diffractive-refractive zone in the center of the lens, with a zone diameter ranging from 3mm to 4.5mm, and a purely refractive outer zone of refractive power compensation. An implantable lens (eg, a refractive-diffractive intraocular lens) may have a monochromatic MTF of 0.43 or better at 100 lp / mm.

[0047] The disclosed exemplary aspects and exemplary embodiments may allow for providing an extended depth of focus that meets the needs of, for example, pseudophakic patients following cataract surgery, particularly with respect to enhancing the patient's range of vision with minimal or no side effects.

[0048] The features and exemplary embodiments described above may also belong to different aspects. BRIEF DESCRIPTION OF THE DRAWINGS

[0049] Other features and advantages will become apparent from the following detailed description considered in conjunction with the accompanying drawings.

[0050] Figure 1 is an exemplary embodiment of an implantable lens according to the first exemplary aspect;

[0051] Figure 2 is an exemplary embodiment of an IOL not according to the first exemplary aspect;

[0052] Figure 3 is an exemplary embodiment of an implantable lens according to the first exemplary aspect;

[0053] Figure 4a is an exemplary diffraction profile of a chromatic aberration-increasing element of an implantable lens according to the first exemplary aspect, in particular a Kinoform lens structure;

[0054] Figure 4b is an exemplary phase diagram (modulo 2π) of an exemplary diffractive surface of an element of the implantable lens inducing chromatic aberration according to the first exemplary aspect, in particular a phase diagram of an exemplary Kinoform lens structure;

[0055] Figure 5a yes Figure 4a / Figure 4b An exemplary modulation transfer function of an exemplary embodiment of

[0056] Figure 5b yes Figure 4a / Figure 4b An exemplary modulation transfer function of an exemplary embodiment of

[0057] Figure 6a is an exemplary diffraction profile of a chromatic aberration-increasing element of an implantable lens according to the first exemplary aspect, in particular a Kinoform lens structure;

[0058] Figure 6b is an exemplary phase diagram (modulo 2π) of an exemplary diffractive surface of an element of the implantable lens inducing chromatic aberration according to the first exemplary aspect, in particular a phase diagram of an exemplary Kinoform lens structure;

[0059] Figure 7a yes Figure 6a / Figure 6b An exemplary modulation transfer function of an exemplary embodiment of

[0060] Figure 7b yes Figure 6a / Figure 6b An exemplary modulation transfer function of an exemplary embodiment of

[0061] Figure 8 is an exemplary phase diagram (modulo 2π) of an exemplary diffractive surface of an element of the implantable lens inducing chromatic aberration according to the first exemplary aspect, in particular a phase diagram of an exemplary Kinoform lens structure;

[0062] Figure 9a yes Figure 8 An exemplary modulation transfer function of an exemplary embodiment of

[0063] Figure 9b yes Figure 8 An exemplary modulation transfer function of an exemplary embodiment of

[0064] Fig.10a is a simulation of a retinal image obtained in an ISO 11979-2 model eye having an implantable lens according to the first exemplary aspect;

[0065] Fig.10b is a simulation of a retinal image obtained in an ISO 11979-2 model eye having an implantable lens according to the first exemplary aspect;

[0066] Fig.10c is a simulation of a retinal image obtained in an ISO 11979-2 model eye having an implantable lens according to the first exemplary aspect;

[0067] Fig.11 is an exemplary logMAR visual acuity;

[0068] Fig.12a An exemplary embodiment of an implantable lens is shown;

[0069] Figure 12b An exemplary embodiment of an implantable lens is shown. DETAILED DESCRIPTION

[0070] The following description is used to deepen understanding and should be understood to supplement the description provided in the above invention summary section of this specification and be read together with the description provided in the above invention summary section of this specification. Some aspects may have different terms than, for example, the terms provided in the above description. However, those skilled in the art will understand that these terms refer to the same subject matter, for example, through more specific expressions. For example, a diffractive structure may be referred to as a diffraction grating; a basic (refractive) power may be referred to as a (nominal) focal length.

[0071] Figure 1An exemplary implantable lens 100 according to a first exemplary aspect is shown, comprising a refractive element 101 causing chromatic aberration and an element causing chromatic aberration increase 102. The element causing chromatic aberration increase 102 comprises a diffractive structure 102, in particular a Kinoform lens structure 102. The refractive element 101 has a front surface 103, and the diffractive structure 102 is located on the front surface 103 (centered on the front surface 103), the axis of rotational symmetry of the Kinoform lens structure about which is the optical axis of the refractive element 101. The refractive element 101 and the element causing chromatic aberration increase 102 together comprise a diffractive-refractive zone 104 centered at the center of the refractive element 101. The diffractive structure 102 is a negative diffractive structure 102. The portion of the refractive element 101 on the surface 103 that is not covered by the diffractive-refractive zone 104 is an outer zone 105, which may for example be only refractive without induced refractive effect and / or without diffractive effect. Alternatively, the diffractive structure 102 comprises a diffractive profile extending from a first Fresnel zone of the diffractive structure to an edge 106 of the diopter, or the diffractive profile extends from a center of the diopter to an edge 106 of the diopter. The implantable lens 100 may be an IOL 100, and the diopter 101 may be a (e.g. plastic) lens 101 having (e.g. plastic) side posts 107 (e.g. haptics 107) to hold the lens in place in a capsular bag within the eye.

[0072] Figure 2 The case where an IOL not according to the first exemplary aspect is implanted in an eye 200 having a refractive element 101 that causes chromatic aberration is shown. Due to the chromatic aberration caused by the refractive element 101, light 203 of different wavelengths λ1, λ2 and λ3 is guided to different focal points 204, 205, 206, for example, blue light 203 of wavelength λ1 (e.g. 450nm) can be guided to focal point 204, green light 203 of wavelength λ2 (e.g. 550nm) can be guided to focal point 205, and red light 203 of wavelength λ3 (e.g. 650nm) can be guided to focal point 206. The optical axis 207 coincides with the rotational symmetry axis of the refractive element 101.

[0073] Figure 3 An exemplary implantable lens 100 according to a first exemplary aspect is shown, the implantable lens 100 comprising a refractive element 101 (which may be Figure 2) and an element 102 causing an increase in chromatic aberration. The element 102 causing an increase in chromatic aberration comprises a diffractive structure 102, in particular a Kinoform lens structure 102. The diffractive element 101 has a front surface 108 and a rear surface 103, wherein the diffractive structure 102 is on the rear surface 103 and is centered at the center of the rear surface 103, i.e. centered on the rear surface 103, so that the axis 207 about which the diffractive structure 102, in particular the Kinoform lens structure 102 is rotationally symmetric coincides with the optical axis 207 of the diffractive element 101. The diffractive structure 102 may be a negative diffractive structure 102. The element 102 causing an increase in chromatic aberration, for example the diffractive structure 102 may cover (almost) the entire rear surface 103, for example the structure may extend from the center of the diffractive element 101 to the edge 106 of the diffractive element 101. The exemplary implantable lens 100 is implanted in an eye 200. Due to chromatic aberration, light 203 of different wavelengths λ1, λ2 and λ3 are directed to different focal points 301, 302, 304, for example blue light 203 of wavelength λ1 (e.g. 450 nm) can be directed to focal point 301 and red light 203 of wavelength λ3 (e.g. 650 nm) can be directed to focal point 304. The optical axis 207 coincides with the axis of rotational symmetry of the refractive element 101. In this example, the implantable lens 100 is implanted in the capsular bag in the eye 200 behind the cornea 201 and the iris 202. The refractive element and the element causing the increase in chromatic aberration direct light about a specific wavelength of light (e.g. about a design wavelength of e.g. 550 nm) to the same focal point. The element 102 causes an increase in chromatic aberration relative to the (intrinsic) chromatic aberration of the refractive element 101. For example, the focal point of the design wavelength λ2 (eg, green light, such as 550 nm, 555 nm, or 456 nm) of the diopter element 101 may be the same as that of the individual diopter elements 101 (eg, Figure 2 Compared with the element 102 that causes the increase in chromatic aberration, the focus of blue light with a wavelength λ1 of 450nm can be shifted closer to the refractive element 101 (relative to the focus of the wavelength λ3 of the refractive element 101 alone), while the focus of red light with a wavelength λ3 of 650nm can be shifted away from the refractive element, so that the distance between the focus of red light and the focus of blue light increases relative to the distance between the focus of red light and the focus of blue light of the refractive element 101 (the element 101 alone without the element 102 that causes the increase in chromatic aberration).

[0074] An implantable lens (e.g., an ophthalmic lens, such as an IOL) according to the first exemplary aspect can induce excess longitudinal chromatic aberration (LCA) to extend the depth of focus (DoF) of the eye, for example, after natural lens removal and (IOL) implantation. Embodiments of the implantable lens according to the first exemplary aspect can increase LCA through refractive and diffractive principles and can be applied to monofocal IOLs, such as standard monofocal IOLs. However, the present application can also be extended to multifocal IOLs to offset the visual quality gap observed between the design foci seen in the current technology. The implantable lens according to the first exemplary aspect can be suitable for standard capsular bag implants as well as supplemental or phakic IOLs.

[0075] Embodiments of implantable lenses according to the first exemplary aspect can be used, for example, to correct aphakia after cataract surgery or refractive lens exchange to provide good distance vision and extend the DOF of the eye. Such embodiments can be, for example, a hybrid lens having a basic (refractive) power, such as a refractive element, and a diffraction grating, such as an element causing an increase in chromatic aberration, which is arranged on the front surface, the back surface, or both surfaces of the hybrid lens.

[0076] In one example, the dioptric element (e.g. a (biconvex) lens) has a pattern of diffractive grooves (e.g. a Kinoform lens structure) located posteriorly (e.g. on the posterior surface of the dioptric element or lens). Such a diffraction grating may have a negative dioptric effect of a lens; thus, the dioptric base power (e.g. of the dioptric element) may be selected to be higher than the nominal focal power to compensate for the reduced focal power. This exemplary embodiment of the implantable lens according to the first aspect may increase the LCA while keeping the blue light focus more anteriorly relative to the central wavelength (i.e. the design wavelength, e.g. 550 nm) compared to a more posterior focus of the red light relative to the central wavelength, which may make it comparable to natural conditions. However, other exemplary embodiments of positive dioptric power with a lower base power and a grating that causes a (excessive) negative LCA may also be used.

[0077] In another exemplary embodiment of the implantable lens according to the first exemplary aspect, the exemplary refractive element has a rear surface and a front surface, the rear surface and the front surface having a spherical shape, wherein the refractive element is similar to a biconvex lens. The exemplary refractive element has a focal power or nominal focal power of 20D. The exemplary element causing an increase in chromatic aberration is (formed on) an exemplary Kinoform lens structure on the rear surface of the exemplary refractive element, the exemplary Kinoform lens structure having, for example, a center thickness of 1 mm. The exemplary Kinoform lens structure has 15 wave zones (e.g., is composed of 15 wave zones). The exemplary refractive element and the exemplary Kinoform lens structure together form an exemplary diffraction-refractive zone centered on the center of the exemplary refractive element. The exemplary element causing an increase in chromatic aberration and the refractive element are composed of the same exemplary material and form an integral unit, the exemplary material having an Abbe number of 46 and a refractive index of 1.50.

[0078] For example, an implantable lens is constructed using a material with a refractive index of 1.50 and an Abbe number of 46. The central lens thickness is assumed to be 1 mm, and a nominal focal power of +20D is set. An eye model can be built in ZEMAX Optic Studio (manufactured by Radial Zemax LLC) according to ISO 11979 to test the optical quality and defocus tolerance of the proposed embodiments. In the case of such tests, optical simulations can be performed in polychromatic light with spectral weightings corresponding to the CIE light efficacy function in the range of 450nm to 650nm.

[0079] In another exemplary embodiment of the implantable lens according to the first exemplary aspect, the exemplary refractive element has a posterior surface and an anterior surface, the posterior surface and the anterior surface having a spherical shape, wherein the refractive element is similar to a biconvex lens. The exemplary refractive element has a basic (optical) focal power or nominal focal power of 23.75D and has a central thickness of 1 mm, for example. The exemplary element causing the increase in chromatic aberration is an exemplary Kinoform lens structure (whose exemplary (radial) profile is formed on) the posterior surface of the exemplary refractive element. Figure 4a / Figure 4b ), the exemplary Kinoform lens structure has a (optical) focal power of -3.75D. The exemplary Kinoform lens structure has 15 wave zones (e.g., is composed of 15 wave zones), wherein the wave zones have a minimum wave zone radius of 0.76 mm (see Figure 4a) and a step height of 6.7 μm. The exemplary refractive element and the exemplary Kinoform lens structure together include an exemplary diffractive-refractive zone centered at the center of the exemplary refractive element. The exemplary Kinoform lens structure utilizes a second diffraction order (m=2). The exemplary chromatic aberration-inducing element and the refractive element are composed of the same exemplary material and form an integral unit, for example, the exemplary material has an Abbe number of 46 and a refractive index of 1.50. In the exemplary chromatic aberration-inducing element, the exemplary increase in chromatic aberration is a two-fold increase (over and above the chromatic aberration caused by the refractive element and the eye). The distance between the focal points between 486 nm and 656 nm light can be increased to 5654 μm when measured in immersion fluid of a surrounding medium with a refractive index of 1.336, and can be increased to 880 μm when measured in the eye / in situ. The refractive elements (without elements that add chromatic aberration) can cause the distance between the focal points of 486nm and 656nm light to be 1364μm when measured in immersion fluid with a surrounding medium having a refractive index of 1.336, and 479μm when measured in the eye / in situ.

[0080] For example, combining a positive refractive substrate with a power of 23.75D with a negative Fresnel lens (-3.75D) effectively doubles the chromatic aberration of a pseudophakic eye. The second diffraction order (m=2) was used, and the diffractive surface consisted of 15 Fresnel zone plates with a minimum zone radius of 0.76 mm (see Figure 6a ). For the choice of m=2, the step height is 6.7 μm, which ensures maximum efficiency. However, if a different (e.g. positive or negative) diffraction order is to be used, the step height can be adjusted accordingly. For example, for the choice of m=1, the first Fresnel zone radius can be 0.54 mm and the step height can be 0.003 mm or 0.0033 mm. The exemplary embodiment depicts a full diffraction design with a grating disposed on the rear surface. Other embodiments with gratings limited to a central lens area (e.g., 3 mm or 4 mm) can allow improved mesopic vision and scotopic vision. The exemplary embodiment can be constructed using a material with a refractive index of 1.50 and an Abbe number of 46. The central lens thickness is assumed to be 1 mm, for example. The chromatic focus shift between 486 nm and 656 nm can be 5654 μm when measured in immersion fluid (the refractive index of the surrounding medium is 1.336). The chromatic focus shift between 486 nm and 656 nm when measured in the eye / in situ may be 880 μm. For a lens without an attached LCA, the chromatic shift may be 1364 μm (immersion fluid) and 479 μm (in situ).

[0081] Figure 4aAn exemplary diffraction profile of an element of an implantable lens causing an increase in chromatic aberration according to the first exemplary aspect is shown, in particular the diffraction profile of a Kinoform lens structure, further details of which can be given by the example above. The step height is 6.7 μm (see sagitta (SAG) shown on the ordinate). The diffraction profile utilizes a 2-fold increase in the longitudinal chromatic aberration of the eye. The diffraction profile is a (continuous) sawtooth surface profile with a local minimum in the center (at radius 0 mm). The baseline of the diffraction profile can follow the surface of the refractive element, so it can be superimposed on the (posterior or anterior) surface of the refractive element. In addition, the distance between the maximum values ​​of the "sawtooths" where the profile reaches the step height decreases with distance from the center. Figure 4b An exemplary phase diagram (modulo 2π) of this exemplary embodiment is shown.

[0082] For example, the element causing the increase in chromatic aberration may be an element causing light to diverge, and Figure 4a The exemplary diffraction profile shown in may be an element causing light divergence and having a negative focal length, in particular a Kinoform lens structure of an implantable lens according to the first exemplary aspect having a lower central zone relative to the first diffraction step.

[0083] The simulated optical quality in the model eye meets the requirements of the manufacturing standard for monofocal lenses (ISO 11979-2), which requires a monochromatic (550nm) modulation transfer function (MTF) greater than or equal to 0.43 at 100 lp / mm. The described exemplary embodiment exceeds this requirement and has an MTF value of 0.66, which indicates near diffraction-limited performance ( Figure 5a ). Figure 5b The multicolor MTF of the discussed embodiment is shown.

[0084] Figure 5a and Figure 5b The modulation transfer function (MTF) levels for an exemplary embodiment are shown for a 2-fold increase in longitudinal chromatic aberration in a model eye. Figure 5a ) and multicolor ( Figure 5b )MTF (solid line) is shown up to 100lp / mm. Dashed line ( Figure 5a ) represents the minimum (monochromatic) MTF of 100 lp / mm acceptable for a monofocal IOL.

[0085] In another exemplary embodiment of the implantable lens according to the first exemplary aspect, the exemplary refractive element has a posterior surface and an anterior surface, the posterior surface and the anterior surface having a spherical shape, wherein the refractive element is similar to a biconvex lens. The exemplary refractive element has a base (optical) power or nominal power of 27.25D. The exemplary chromatic aberration-inducing element is an exemplary Kinoform lens (whose exemplary (radial) profile is formed on the posterior surface of the exemplary refractive element) Figure 6a / Figure 6b ), an exemplary Kinoform lens structure has a (optical) power of -7.25 D. An exemplary Kinoform lens structure has 30 wave zones (e.g., composed of 30 wave zones), wherein the wave zones have a minimum wave zone radius of 0.55 mm (see Figure 6a ) and a step height of 6.7 μm. The exemplary refractive element and the exemplary Kinoform lens structure together form an exemplary diffractive-refractive zone centered at the center of the exemplary refractive element. The exemplary Kinoform lens structure utilizes a second diffraction order. The exemplary chromatic aberration-inducing element and the refractive element are composed of the same exemplary material and form an integral unit, the exemplary material having an Abbe number of 46 and a refractive index of 1.50. In the exemplary chromatic aberration-inducing element, the exemplary chromatic aberration increase is a three-fold increase (over and above the chromatic aberration caused by the refractive element and the eye). The distance between the focal points between 486 nm and 656 nm light can be increased to 9722 μm when measured in immersion fluid with a refractive index of the surrounding medium of 1.336, and can be increased to 1247 μm when measured in the eye / in situ. The refractive elements (without elements that add chromatic aberration) can cause the distance between the focal points of 486nm and 656nm light to be 1364μm when measured in immersion fluid with a surrounding medium having a refractive index of 1.336, and 479μm when measured in the eye / in situ.

[0086] For example, combining a positive refractive substrate with a power of 27.25D with a negative Fresnel lens (-7.25D) effectively triples the chromatic aberration of a pseudophakic eye. The second diffraction order (m=2) was used, and the diffractive surface consisted of 30 Fresnel zone plates with a minimum zone radius of 0.55 mm ( Figure 3). For the choice of m=2, the step height is 6.7 μm, which can ensure maximum efficiency. However, if a different (e.g., positive or negative) diffraction order is to be used, the step height can be adjusted accordingly. For example, for the choice of m=1, the first Fresnel zone radius can be 0.39 mm and the step height can be 0.003 nm or 0.0033 mm. This exemplary embodiment depicts a full diffraction design with a grating disposed on the rear surface. Other embodiments with gratings limited to a central lens area (e.g., 3 mm or 4 mm) can allow improved mesoscopic vision and scotopic vision. This exemplary embodiment can be constructed using a material with a refractive index of 1.50 and an Abbe number of 46. The central lens thickness is assumed to be 1 mm, for example. The chromatic focus shift between 486 nm and 656 nm measured in immersion fluid (the refractive index of the surrounding medium is 1.336) can be 9722 μm. The chromatic focus shift between 486 nm and 656 nm when measured in the eye / in situ can be 1247 μm. For the lens without the attached LCA, the color shift can be 1364 μm (immersion fluid) and 479 μm (in situ).

[0087] Figure 6a An exemplary diffraction profile of an exemplary chromatic aberration-inducing element of an implantable lens according to the first exemplary aspect, in particular a Kinoform lens structure, is shown, further details of which can be given by the examples above. The diffraction profile exploits a 3-fold increase in the longitudinal chromatic aberration of the eye. The diffraction profile is a continuous "sawtooth" surface profile with a local minimum at the center (radius 0 mm). The baseline of the diffraction profile follows the surface of the refractive element, so it is superimposed on the (posterior or anterior) surface of the refractive element. In addition, the distance between the maximum values ​​of the "sawtooth" where the profile reaches the step height decreases as it moves away from the center. Figure 6b An exemplary phase diagram (modulo 2π) of this exemplary embodiment is shown.

[0088] For example, the element causing the increase in chromatic aberration may be an element causing light to diverge, and Figure 6a The exemplary diffraction profile shown in may be an element causing light divergence and having a negative focal length, in particular a Kinoform lens structure of an implantable lens according to the first exemplary aspect having a lower central region relative to the first diffraction step.

[0089] The simulated optical quality in the model eye met the requirements of the manufacturing standard for monofocal lenses (ISO 11979-2), which is a monochromatic (550nm) modulation transfer function (MTF) greater than or equal to 0.43 at 100 lp / mm. The described exemplary embodiment exceeds this requirement and has an MTF value of 0.65, which indicates near diffraction-limited performance ( Figure 7a ). Figure 7bThe multicolor MTF of the discussed embodiment is shown.

[0090] Figure 7a and Figure 7b The modulation transfer function (MTF) levels of an exemplary embodiment are shown for a 3-fold increase in longitudinal chromatic aberration in a model eye. Figure 7a ) and multicolor ( Figure 7b )MTF (solid line) is shown up to 100lp / mm. Dashed line ( Figure 7a ) represents the minimum (monochromatic) MTF of 100 lp / mm acceptable for a monofocal IOL.

[0091] In another exemplary embodiment of the implantable lens according to the first exemplary aspect, the exemplary refractive element has a posterior surface and an anterior surface, the posterior surface and the anterior surface having a spherical shape, wherein the refractive element is similar to a biconvex lens. The exemplary refractive element has a base (optical) power or nominal power of 23.5D. The exemplary element causing the increase in chromatic aberration is an exemplary Kinoform lens structure (see FIG. 1 ) on the posterior surface of the exemplary refractive element. Figure 8 Phase diagram in (modulo 2π), the exemplary Kinoform lens structure has a (optical) focal power of -3.5D. The exemplary Kinoform lens structure has 14 wave zones (e.g., is composed of 14 wave zones), wherein the wave zones have, for example, a minimum wave zone radius of 0.8mm and a step height of 6μm. The exemplary element causing the increase in chromatic aberration and the refractive element are composed of the same exemplary material and form an integral unit, the exemplary material having an Abbe number of 42 and a refractive index of 1.52. In the exemplary element causing the increase in chromatic aberration, the increase in exemplary chromatic aberration is a two-fold increase (over and above the chromatic aberration caused by the refractive element and the eye). For example, combining a positive refractive substrate with a focal power of 23.5D with a negative Fresnel lens (-3.5D) effectively doubles the chromatic aberration of a pseudophakic eye. A second diffraction order (m=2) is used, and the diffractive surface is composed of 14 Fresnel wave zone plates, wherein the minimum wave zone radius is 0.8mm. For the choice of m=2, the step height is 6μm, which ensures maximum efficiency. However, if a different (e.g., positive or negative) diffraction order is to be used, the step height can be adjusted accordingly. For example, for the choice of m=1, the first Fresnel zone radius can be 0.57mm and the step height can be 0.003mm or 0.0033mm. The exemplary embodiment depicts a full diffraction design with a grating disposed on the rear surface. Other embodiments with gratings limited to a central lens area (e.g., 3mm or 4mm) can allow improved medium light vision and dark light vision. The exemplary embodiment can be constructed using a material with a refractive index of 1.52 and an Abbe number of 42. The central lens thickness is assumed to be 1mm, for example.

[0092] The phase profile of the diffraction surface is Figure 8 , which shows a phase diagram of a fully diffractive surface (modulo 2π). However, in other exemplary embodiments, the diffraction grating may, for example, be limited to a central lens area (e.g., 3 mm or 4 mm, e.g., see Figure 12b ).

[0093] Figure 9a and Figure 9b The modulation transfer function (MTF) levels for an exemplary embodiment (previously described exemplary embodiment) with longitudinal chromatic aberration increased by a factor of 2 in a model eye are shown. Monochrome (550nm, Figure 9a ) and multicolor ( Figure 9b )MTF (solid line) is shown up to 100lp / mm. Dashed line ( Figure 9a ) represents the lowest (monochromatic) MTF at 100 lp / mm acceptable for a monofocal IOL, and the dashed line represents the diffraction limited modulation transfer (MT).

[0094] The simulated optical quality in the model eye meets the requirements of the manufacturing standard for monofocal lenses (ISO 11979-2), which requires a monochromatic (550nm) modulation transfer function (MTF) greater than or equal to 0.43 at 100 lp / mm. The described exemplary embodiment exceeds this requirement and has an MTF value of 0.58 and has a nearly diffraction-limited performance ( Figure 9a ). Figure 9b The multicolor MTF of the discussed embodiment is shown.

[0095] Fig.10a , Fig.10b and Fig.10c According to the first aspect (characterized in that LCA is increased by 2 or 3 times), the above exemplary embodiments (respectively referring to Figure 4a / Figure 4b and Figure 6a / Figure 6b ) in the ISO 11979-2:2014 model eye. Comparison of monochromatic and polychromatic (with spectral weighting) conditions shows a significant increase in DoF due to chromatic aberration. Retinal image simulation in Figure 8 a. Figure 8 b and Figure 8 c is presented with corresponding defocus values. A 3-fold increase in LCA results in comparable image quality over the 2D range (from -1D to +1D). Intentional myopic refractive targeting can extend the useful visual range. This IOL can also provide a larger "landing zone", which can allow for better refractive outcomes after surgery.

[0096] Fig.11Simulated logMAR visual acuity under three conditions of defocus ranging from +1 D to -2 D are shown. The vertical dashed line indicates the position of best far focus.

[0097] Below, the quantification of the extended depth of focus is described:

[0098] The natural 2x and 3x LCA conditions can be compared based on their image quality metrics at a 3mm pupil. To this end, the area under the MTF (MTFa) can be obtained based on the following formula:

[0099]

[0100] where d determines the sampling of the spatial frequency (f). MTFa can be derived for each defocus position from +1D to -2D and converted to clinical visual acuity according to the following model:

[0101] VA=a·MTFa b +c

[0102] The coefficients used in the calculation can be taken from ANSI Z80.35-2018 (a = 0.085, b = -1.0, and c = -0.21). Fig.11 In, three conditions in terms of simulated visual acuity were compared. At the best far focus (0D), a 2-fold LCA increase only resulted in a visual acuity change of 0.02logMAR, and a 3-fold LCA increase resulted in a visual acuity change of 0.05logMAR. However, the predicted visual acuity level is still better than the average value of the normal population (i.e., 0.00logMAR or 20 / 20 Snellen). The natural LCA model proves that the optical quality deteriorates more significantly than the IOL with increased LCA when defocused. For example, at 1.50D (viewing distance 67cm), doubling the LCA of the eye increases visual acuity by 0.07logMAR, but when the LCA is tripled, the visual acuity increases by 0.11logMAR.

[0103] Fig.12a and Figure 12b A further exemplary embodiment of an implantable lens is shown, which comprises a refractive element causing chromatic aberration and an element causing an increase in chromatic aberration, wherein the element causing the increase in chromatic aberration comprises a diffractive structure, in particular the diffractive structure is a Fresnel structure, in particular a Kinoform lens structure, wherein the diffractive structure comprises a diffraction profile, and wherein in particular the diffraction profile extends from a first Fresnel wave zone of the diffractive structure to an edge of the refractive element. Fig.12a , Figure 12b The structure shown can be used, for example, with respect to Figure 8 , Figure 9a and Figure 9bThe described exemplary embodiments are used in combination.

[0104] exist Fig.12a In one exemplary option shown in , the design of the implantable lens is, for example, fully diffractive, wherein the diffractive structures (Fresnel rings) extend to the edge of the lens. Figure 12b In another exemplary option shown in , the design of the implantable lens is, for example, partially diffractive, where the diffractive structures (Fresnel rings) extend to a diameter of 3 mm, 4 mm, or 4.5 mm, which can improve low-light vision / medium-light vision and can also facilitate manufacturability. Fig.12a and Figure 12b In the crystalline lens, the Kinoform structure is a negative Kinoform structure, and its diffraction profile extends from the center to the edge of the lens ( Fig.12a ) or extends to a specific distance from the center ( Figure 12b ). Fig.12a and Figure 12b The Kinoform lens structure in is a (continuous) "sawtooth" surface profile with a local minimum at the center (at radius 0 mm, i.e. X=Y=0 mm). The "sawtooth" has a maximum value (depicted as concentric solid lines) where the profile reaches the step height, which decreases as it moves away from the center.

[0105] The expression "A and / or B" is considered to include any of the following three situations: (i) A, (ii) B, (iii) A and B. In addition, the article "a" should not be understood as "one", that is, the use of the expression "element" does not exclude the presence of other elements. The term "comprising" should be understood in an open sense, that is, in a way that the object of "comprising element A" also includes other elements in addition to element A. In addition, the term "comprising" can be limited to "consisting of...", that is, consisting only of the specified elements. The expression "A and / or B" can also be understood to mean "at least one of A and B" or "at least one of the following: A and B".

[0106] It will be understood that all presented embodiments are examples only, and any feature presented for a particular exemplary embodiment may be used alone or in combination with any feature presented for the same or another particular exemplary embodiment and / or in combination with any other feature not mentioned, together with any aspect. In particular, the exemplary embodiments presented in this specification should also be understood to be disclosed in all possible combinations with each other, as long as they are technically reasonable and the exemplary embodiments are not alternatives to each other. It will also be understood that any feature presented for an exemplary embodiment in a particular category (method / device / computer program / system) may also be used in a corresponding manner in any other category of exemplary embodiments. It should also be understood that the presence of a feature in the presented exemplary embodiment should not necessarily mean that the feature forms a necessary feature and cannot be omitted or replaced.

[0107] The statement that a feature comprises at least one of the subsequently listed features does not necessarily mean that the feature comprises all of the subsequently listed features, or at least one of a plurality of subsequently listed features. Furthermore, the listed features may be selected in any combination, or only one of the listed features may be selected. Specific combinations of all of the subsequently listed features are also conceivable. Moreover, a plurality of only one of the listed features is possible.

[0108] The order of all method steps presented above is not mandatory, alternative orders are possible. However, the specific order of method steps as laid out in the wording of the claims or in the above description should be considered as one possible order of the method.

[0109] The present subject matter has been described above by way of exemplary embodiments. It should be noted that there are alternatives and modifications that are obvious to those skilled in the art and that can be implemented without departing from the scope of the appended claims.

Claims

1. An implantable lens comprising a refractive element causing chromatic aberration and an element causing an increase in chromatic aberration, wherein the element causing an increase in chromatic aberration comprises a diffractive structure, wherein the diffractive structure is a negative diffractive structure, and wherein the diffractive structure is a Kinoform lens structure.

2. The implantable lens according to claim 1, wherein: The increase in color difference is an increase of at least two times, preferably at least three times, in particular a factor of between three and seven times.

3. The implantable lens according to claim 1 or 2, wherein: The refractive element has a rear surface and a front surface, and the rear surface and / or the front surface has an aspherical shape or a spherical shape.

4. An implantable lens according to any one of claims 1 to 3, wherein: The element causing the increase in chromatic aberration increases the distance between the focus of red light with a wavelength of 650 nm and the focus of blue light with a wavelength of 450 nm to 5 mm to 13 mm under standard room conditions; and / or the element causing the increase in chromatic aberration increases the distance between the focus of 656 nm red light and the focus of 486 nm blue light by between 5 mm and 10 mm when measured in vitro or in immersion fluid, wherein the immersion fluid has a refractive index of 1.333; and / or the element causing the increase in chromatic aberration increases the distance between the focus of 656 nm red light and the focus of 486 nm blue light by between 0.8 mm and 1.3 mm when measured in vivo or in situ; and in particular, the refractive element causes chromatic aberration, wherein the distance between the focus of red light and the focus of blue light is between 1 mm and 2 mm when measured in vitro or in the immersion fluid, and / or is between 0.4 mm and 0.6 mm when measured in vivo or in situ.

5. The implantable lens according to claim 4, wherein: The refractive element has a rear surface and a front surface, and the diffractive structure is on the rear surface and / or the front surface.

6. The implantable lens according to claim 4 or 5, wherein: The diffractive structure has a focal power of at most -1D, in particular the focal power is between -1D and -11D.

7. An implantable lens according to any one of claims 4 to 6, wherein: The diffractive structure comprises a diffractive profile, and wherein in particular the diffractive profile extends from a first Fresnel zone of the diffractive structure to an edge of the dioptric element, or the diffractive profile extends from a center of the dioptric element to an edge of the dioptric element.

8. An implantable lens according to any one of claims 1 to 7, wherein: The dioptric element and the element causing an increase in chromatic aberration together comprise a diffractive-dioptric zone centered on the center of the dioptric element, in particular the diffractive-dioptric zone has a diameter of 3 mm to 4.5 mm.

9. An implantable lens according to any one of claims 1 to 8, wherein: The diffractive structure utilizes a first diffraction order and / or a second diffraction order.

10. An implantable lens according to any one of claims 1 to 9, wherein: The diopter element has a nominal focal power range of -5D to 40D.

11. An implantable lens according to any one of claims 1 to 10, wherein: The element causing an increase in chromatic aberration increases the chromatic aberration by at least 1D, preferably at least 2D, in the spectral range of 450 nm to 650 nm.

12. An implantable lens according to any one of claims 1 to 11, wherein: The element causing an increase in chromatic aberration and the dioptric element consist of the same material, in particular, the element causing an increase in chromatic aberration and the dioptric element form an integral unit.

13. An implantable lens according to any one of claims 1 to 12, wherein: The Kinoform lens structure comprises a sawtooth surface profile, which is in particular superimposed on the front surface and / or the back surface of the refractive element, wherein optionally the Kinoform lens structure can have a central zone which is lower with respect to the first diffractive step.

14. The implantable lens of claim 13, wherein: The sawtooth surface profile has a local minimum in the center and, in particular, the distance between the maximum values ​​where the sawtooth surface profile reaches step heights decreases moving away from the center of the diopter element.

15. A method for producing an implantable lens according to any one of claims 1 to 14, said method comprising etching and / or machining elements causing an increase in chromatic aberration on the front and / or rear surface of the refractive element.

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