Accommodative intraocular lens with variable aberration combination for extended depth of field - Patents.com

Abstract

The present invention relates to an accommodating intraocular lens having an optical axis 5. The lens comprises at least two optical elements 1, 2 and haptics enabling mutual translational movement of said elements in a direction 3 substantially perpendicular to the optical axis, at least two elements each comprising a freeform optical surface. The invention also relates to the combination of such a lens with a device configured to measure the optical output of an eye.

Description

[Technical field]

[0001] (summary) The accommodative lens provides a combination of variable defocus and a desired variable depth of field. Or alternatively, the lens provides a combination of variable defocus and accommodation of variable undesired optical aberrations. The freeform optical surface for variable light output can be provided by laser treatment of the implanted lens pre-operatively, during manufacture, or alternatively post-operatively. [Background technology]

[0002] (Main text) This document, i.e. the present specification, discloses the accommodation of accommodative intraocular lenses (hereinafter also referred to as "lenses") implanted in a human eye. Detailed descriptions of such lenses and their accommodation are disclosed in numerous documents, for example in Dutch Patent Publication 2012133, Dutch Patent Publication 201242, European Patent Publication 1871299, European Patent Publication 1932492 and related publications for the design of such accommodative intraocular lenses (AIOLs), and in Alio in Am J Ophthamol 2016 Apr, 164: 37-48 for clinical results. These documents, including but not limited to those cited herein, and all references made therein, are considered to be part of this specification. This specification discloses a variable focus lens (hereinafter also referred to as a "lens"). The lens has an optical axis and at least two optical elements, each of which has at least one freeform optical surface. Each optical element preferably has at least one Alvarez, cubic optical surface. Such lenses change the optical output and thus the "defocus", the degree of which depends primarily on the degree of relative movement of the optical elements in a direction perpendicular to the optical axis. In addition, the variable-focus lens also includes a wavefront encoding phase mask (hereinafter also referred to as the "mask"). The mask is a free-form By gradually varying the steepness of the cubic optical surface, the output of the cubic term is varied, thus providing an extended depth of field (EDOF). A cubic phase mask, or alternatively a gradually varying, e.g., modulated cubic phase mask with increasing third order terms, are preferred embodiments of the mask. Variable depth of field extension can also be achieved by alternative mask designs with optical surfaces combining other surfaces of other Zernike orders. For example, a variable aspheric surface, at least two freeform optical surfaces for variable aspheric aberration providing spherical aberration, can be added to the cubic surface providing variable defocus. The effect of spherical aberration on the depth of field is discussed in, for example, Mouroulis's "Using Spherical Optics" Mouroulis, “Depth of field extension with spherical optics”, See Optics Express, August 2008, Vol. 16, No. 17.

[0003] Cubic wavefront coded phase masks for depth of field extension are best known for depth of field extension, as described in technical applications such as, for example, European Patent Publication No. 2110702 and U.S. Patent Publication No. 6,547,139. ​​The main invention of cubic phase coding was published by E.R. Dowski, Jr. and W.T. Cathey in the paper entitled "Depth of Field Extension by Wavefront Coding" (1999). "Extended depth of field through wavefront coding" in Appl. Opt. 34(11), 1859-1866 (1995), and, for example, U.S. Pat. No. 5,748,371 and International Publication No. This has been reported in many accompanying patent documents, such as US Pat. No. 99 / 57599. The mask preferably adjusts the phase of the light, not the amplitude of the light. The mask is a cubic mask that modifies the third order terms, or alternatively an aspheric mask that modifies the aspheric terms, as long as the optical mask maintains the magnification of the optical transfer function. This magnification may be a fixed magnification, or alternatively a variable magnification, as described herein, where the range of magnification depends primarily on the shift of the mask in a direction perpendicular to the optical axis.

[0004] Depth of field is the focus Shin It is noted that the depth of field extension increases the focal length, but by definition it also increases the blur and therefore the loss of contrast, especially for high spatial frequencies. The depth of field extension widens the "focal tunnel", the range of acceptable focus along the optical axis. This tunnel changes from "short and narrow", meaning a sharp focus with a short depth of field, to "long and wide", meaning a blurred focus with a long depth of field. Whether the depth of field extension is an advantage outweighs the disadvantage of the loss of contrast in the requirements of a particular application of the lens, and the degree (percentage) of the extension can be calculated and incorporated into the design of the mask. For example, it is said that human vision requires a high sharpness of 0.8 or more to see far away, but the visual acuity for reading close up falls to 0.4. An accommodative intraocular lens that provides such an "asymmetric depth of field extension" can be designed in a manner as disclosed herein.

[0005] For example, the movement of the optical element for an accommodative intraocular lens can be achieved by principles such as those disclosed in US2009 / 062912 and WO2005 / 084587, and similar concepts with various accommodations are disclosed in, but not limited to, the following patent documents: US2014 / 074233, WO2014 / 058316, EP2765952, NL2012 / 257278, US2010 / 131955, US2010 / 106245, and NL1029548. These principles have been shown to work well for both spectacles and accommodative intraocular lenses, for the human eye as well as for camera applications.

[0006] Such accommodative intraocular lens applications are for example ophthalmic applications for spectacles and for intraocular lenses implanted in the human eye. Such accommodative, translating intraocular lens structures are also known from other sources, for example the designs of such structures are known from Dutch Patent Publication 2012133, Dutch Patent Publication 201242, European Patent Publication 1871299, European Patent Publication 1932492, and clinical results are known from, for example, Alio et al., Am J Ophthamol 2016 Apr, 164: 37-48. [Prior art documents] [Patent documents]

[0007] [Patent Document 1] Netherlands Patent Publication No. 2012133 [Patent Document 2] Netherlands Patent Publication No. 201242 [Patent Document 3] European Patent Publication No. 1871299 [Patent Document 4] European Patent Publication No. 1932492 [Patent Document 5] European Patent Publication No. 2110702 [Patent Document 6] U.S. Patent Publication No. 6,547,139 [Patent Document 7] U.S. Patent Publication No. 5,748,371 [Patent Document 8] International Publication No. 99 / 57599 [Patent Document 9] US Patent Application Publication No. 2009 / 062912 [Patent Document 10] International Publication No. 2005 / 084587 [Patent Document 11] US Patent Application Publication No. 2014 / 074233 [Patent Document 12] International Publication No. 2014 / 058316 [Patent Document 13] European Patent Publication No. 2765952 [Patent Document 14] Dutch Patent Application Publication No. 2012 / 257278 [Patent Document 15] US Patent Application Publication No. 2010 / 131955 [Patent Document 16] US Patent Application Publication No. 2010 / 106245 [Patent Document 17] Netherlands Patent Publication No. 1029548 [Patent Document 18] International Publication No. 2018 / 152407 [Non-patent literature]

[0008] [Non-Patent Document 1] Alio et al., Am J Ophthamol 2016 Apr, 164: 37-48 [Non-Patent Document 2] Mouroulis, “Depth of field extension with spherical optics”, Optics Express, August 2008, Vol.16, No. 17 [Non-Patent Document 3] Dowski, Jr., E.R. and Cathey, W.T. "Extended depth of field through wavefront coding" Appl. Opt. 34(11), 1859-1866 (1995) Summary of the Invention

[0009] This specification discloses lenses that provide a combination of variable defocus and a desired variable depth of field, or alternatively, a combination of variable defocus and adjustment of variable undesirable optical aberrations.

[0010] The lens has an optical axis and comprises at least two optical elements, at least one of which translates in at least one direction mainly perpendicular to the optical axis. Each optical element comprises at least one free-form optical surface, the combination of which provides a change in at least one optical aberration of the lens. The degree (percentage) of this change in optical aberration depends on the degree (percentage) of the shift of at least one of the optical elements. Such translating lenses are known from the aforementioned documents, and such lenses usually, but not necessarily, have cubic optical surfaces to provide a variable defocused output. Such cubic surfaces, additional optical surfaces, and combinations of surfaces can be defined by Zernike polynomials, the first 15 modes of which are believed to be relevant to the human eye, and which polynomials are described herein to describe free-form optical surfaces of various optical surface shapes. Such optical surfaces, such free-form optical surfaces, rotationally asymmetric optical surfaces can be, for example, spline, or Cartesian, or non-uniformly weighted B-spline (NUR) optical surfaces. The cubic surfaces may be derived from the 3D 3D (BS) algorithm, or any other algorithm. Freeform surfaces derived from any formula or algorithm are considered to be included herein. An example of such a cubic surface is a surface according to the formula: t1=A(xy 2 +1 / 3x 3)+E

[0011] The optics of such a lens provide variable focus, primarily to accommodate the eye. That is, it provides variable defocus to correct the defocus aberration of the eye to provide clear vision from far to near reading distances. The translation of at least one of the optical elements is a shift, meaning a slide of the optical element in a direction perpendicular to the optical axis, or alternatively a rotation in a plane perpendicular to the optical axis, or alternatively a wedging of the optical element. , or alternatively any combination of movements in a plane primarily perpendicular to the optical axis.

[0012] The lens can include at least one fixation haptic, where a haptic is a haptic that positions and fixates the optic within the anterior chamber of the eye, or alternatively, within the posterior chamber of the eye. The opportunity A lens may include at least one haptic for providing a combination of positioning and translation. The lens may include at least one haptic coupled to a natural component of the eye. This component may be the ciliary mass of the eye or alternatively the zonular network of the eye or alternatively the capsular bag of the eye or alternatively the iris of the eye or alternatively any natural component of the eye. The lens may also be actuated by hydraulic pressure generated in the posterior chamber of the eye, or alternatively by a MEMS, which stands for Micro-Electro-Mechanical System, which provides the translation of at least one optical element. Furthermore, the lens may also comprise at least one optical surface for correcting a fixed optical defect of the eye, such as, for example, presbyopia (also called reading hyperopia), which is a fixed optical defect. The lens may also correct at least one undesirable variable optical defect of the eye, such as, for example, variable astigmatism, or alternatively, variable spherical aberration, which is an undesirable aberration that may be generated by an optical surface of the eye or, alternatively, an optical surface of the lens.

[0013] TIFF0007623067000001.tif152170

[0014] Optical surfaces for providing additional variable light output can be added to the lens during manufacture of the lens prior to implantation based on the degree (percentage) of variable light output based on pre-operative measurements of the eye in which the lens is to be implanted. Alternatively, optical surfaces for providing additional variable light output can be added post-implantation based on the degree (percentage) of variable light output based on post-operative measurements of the eye in which the lens is to be implanted. Modification of optical surfaces can be provided, for example, by post-operative laser treatment of intraocular material as described in WO 2018 / 152407, customized wavefront-induced refractive laser treatment of the accommodative intraocular lens after surgery. Optical surface modification treatments for at least one of the variable aberrations described herein can be performed. Such treatments can adjust optical surfaces to provide variable defocus, for example by increasing the steepness of these surfaces to increase the diopter change per unit of mutual translational movement of the optical surfaces.

[0015] Preferably, the additional freeform surface is configured to provide a variably increased additional light output depending on the rate of mutual translation of the elements.

[0016] In an attractive embodiment, the additional freeform surface is configured to variably reduce the additional light output depending on the rate of mutual translation of the elements.

[0017] Preferably, the additional freeform surface varies the additional light output providing an increased depth of field of the lens. It is configured to make

[0018] In another attractive embodiment, the additional freeform surface provides the feature that it is configured to vary the additional light output that provides a reduction in the depth of field of the lens.

[0019] The additional freeform surface may also be configured to provide an astigmatic variable light output.

[0020] The additional freeform surface is preferably configured to provide an aspheric variable light output.

[0021] According to another possibility, the additional freeform surface is configured to provide an arbitrary variable output of any Zernike mode.

[0022] The additional freeform optical surface may also be configured to provide a combination of variable optical outputs of any of a number of Zernike modes.

[0023] The invention also provides a combination of a lens as claimed in any one of claims 1 to 9 with a device configured to measure the light output of an eye comprising the artificial lens and configured to convert the measured light output into a light output of the artificial lens.

[0024] Preferably, the apparatus is configured to measure the eye including measuring a range of light output change of at least one variable aberration of the eye into which the lens is implanted, and configured to convert said light output change into a diopter change for the same aberration provided by at least two freeform optical surfaces of the lens.

[0025] The device may also be configured to perform measurements of an eye having the lens implanted therein, including providing measurements of a range of diopter changes of at least one additional variable aberration, converting said diopter changes into diopter changes for the same aberration provided by at least two freeform optical surfaces of the lens, and adjusting said diopter changes of the freeform surfaces by any post-operative freeform change procedure.

[0026] According to one embodiment, the device is configured to manufacture the lens before implantation begins.

[0027] However, the device may also be configured to perform post-operative freeform deformation procedures.

[0028] More specifically, the device is configured to perform post-operative in situ laser therapeutic freeform modification procedures on the lens. [Brief description of the drawings]

[0029] (drawing) [Figure 1] FIG. 1 is a diagram showing an embodiment of an extended depth of field for an accommodative lens having an additional freeform surface for variable aspheric aberration. FIG. 1 is a diagram of the prior art for explaining the present invention of FIG. [Diagram 2] FIG. 2 is an illustration showing one embodiment of an extended depth of field for an accommodative lens having an additional freeform surface for variable aspheric aberration. FIG. 2 is an illustration of the prior art for explaining the present invention of FIG. 3. [Diagram 3] FIG. 1 illustrates an embodiment of the present invention of depth of field extension for an accommodative lens with additional freeform surface for variable aspheric aberration. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0030] Figure 1 shows a non-aberrated, fully accommodative lens, which can be described as an optical system with a sharp focus over a desired range. The lens comprises two optical elements 1, 2 which translate in a direction 3 primarily perpendicular to the optical axis, providing a focus 7 for near vision with an incoming light beam 4, an optical axis 5, an outgoing focused light beam 6, and after translational movement of at least one of the optical elements, the lens provides a focus 9 for far vision with an outgoing focused light beam 8 and a focal range 10 of the lens.

[0031] Figure 2 shows a fixed aberration optical system with a fixed blurred focus, with blur 11 to add extended depth of field 13a for near vision, which is desirable, but also adding blur 13b for distance vision, which is generally undesirable because distance vision is more sensitive to image degradation than near vision. This figure shows, for example, the effect of adding a fixed power aspheric to a fixed focus lens over a desired range, with blur indicated by the extended focus, or focal tunnel 12.

[0032] Figure 3 shows an example of the invention, a variable aberration optical system with a variable blur focus, for example a variable aspheric addition to a variable focus lens, which firstly provides a blur 16 that expands the desired range 13a in near vision, secondly adjusts the blur to gradually reduce the focal tunnel, and thirdly provides a clear focus 15 in far vision while maintaining the expanded focal range 17 as in Figure 2.

[0033] In summary, the present specification discloses an accommodative intraocular lens having an optical axis, the lens comprising at least two optical elements, at least one of which is configured to translate in at least one direction substantially perpendicular to the optical axis, at least two of which have at least one freeform optical surface each configured to provide a variable defocused light output, the degree (percentage) of the light output depending on the degree (percentage) of the mutual shift of the elements, each element also having at least one additional freeform optical surface configured to provide a variable light output of at least one additional aberration other than defocus, the degree (percentage) of the variable light output of the additional aberration depending on the degree (percentage) of the mutual shift of the elements. The additional freeform surface can variably increase the additional variable light output depending on the degree (percentage) of mutual shift of the elements, or alternatively, the additional freeform surface can variably decrease the additional variable light output depending on the degree (percentage) of mutual shift of the elements. For example, the additional freeform surface can vary the additional variable light output providing an extension of the depth of field of the lens, or alternatively, the additional freeform surface can vary the additional variable light output providing a reduction of the depth of field of the lens. The additional freeform surface can provide an astigmatic variable light output, or alternatively, can provide an aspheric variable light output, or alternatively, can provide any variable output of any Zernike mode, or alternatively, can provide a combination of multiple variable light outputs of any multiple Zernike modes.

[0034] A method of providing such a lens can be a pre-operative method comprising: first, providing measurements of an eye into which the lens is to be implanted, the measurements including measuring a range of diopter changes of at least one variable aberration, second, converting said diopter changes into diopter changes for the same aberrations provided by at least two freeform optical surfaces of the lens, and third, providing for the manufacture and implantation of the lens. Alternatively, the method of providing such a lens can be a post-operative method, comprising: first, performing measurements of an eye implanted with the lens, including measuring a range of diopter changes of at least one additional variable aberration, second, converting said diopter changes to diopter changes for the same aberrations provided by at least two freeform optical surfaces of the lens, and third, converting said diopter changes of the freeform surfaces by any post-operative freeform modification procedure. The optional post-operative freeform change procedure can be any procedure, for example, post-operative modification of intraocular materials by laser treatment, such as femtosecond laser treatment.

[0035] A method of providing such a lens can be, but is not limited to, providing an increase in diopter change of any aberration per unit of translational movement of the optical element, such as, for example, an increase in aspheric aberration, to provide the desired depth of field extension, as illustrated in FIGS. 1-3.

[0036] Alternatively, a method of providing such a lens may provide a reduction in the diopter change of any aberration per unit of translational movement of the optical element, such as, for example, a reduction in undesirable variable coma aberration or a reduction in any undesirable variable aberration that reduces the visual acuity of the eye.

[0037] The invention further relates to a combination of a lens according to the invention with a device configured to measure the light output of an eye equipped with the artificial lens and configured to convert the measured light output into a light output of the artificial lens.

[0038] In one embodiment, the device is configured to measure an eye including measuring a range of light output change of at least one variable aberration of the eye into which the lens is implanted, and configured to convert said light output change into a diopter change for the same aberration provided by at least two freeform optical surfaces of the lens.

[0039] In one embodiment (which may be combined with other embodiments of the invention), the device is configured to perform measurements of an eye implanted with a lens, including providing measurements of a range of diopter changes of at least one additional variable aberration, converting said diopter changes to diopter changes for the same aberrations provided by at least two freeform optical surfaces of the lens, and adjusting said diopter changes of the freeform surfaces by any post-operative freeform change procedure.

[0040] In one embodiment (which may be combined with other embodiments of the invention), the apparatus is configured to manufacture a lens.

[0041] In one embodiment (which may be combined with other embodiments of the present invention), the device is configured to perform a post-operative freeform modification procedure.

[0042] In one embodiment (which may be combined with other embodiments of the invention), the device is configured to perform post-operative in-situ laser therapeutic freeform modification procedures.

Claims

1. An accommodative intraocular lens having an optical axis, the lens comprising: two optical elements; and haptics that permit relative translational movement of the two optical elements in a direction substantially perpendicular to the optical axis; each of the two optical elements has a first free-form optical surface configured to variably increase or decrease a defocusing capability in response to a magnitude of mutual translation of the two optical elements in the direction in order to correct aberrations that cause defocusing of the eye; An accommodative intraocular lens characterized in that each of the two optical elements has a second free-form optical surface formed to variably increase or decrease an optical output characteristic based on an additional aberration other than the aberration that causes the defocus, corresponding to the magnitude of relative translational movement of the two optical elements in the direction, and the second free-form optical surface is formed to variably set the depth of field of the lens by varying the additional aberration.

2. The lens of claim 1 , wherein the second freeform optical surface is configured to change an optical output characteristic of the lens to increase a depth of field of the lens.

3. The lens of claim 1 , wherein the second freeform optical surface is configured to change an optical output characteristic of the lens to reduce a depth of field of the lens.

4. The lens of claim 1 , wherein the second freeform optical surface is configured to provide a variable optical output characteristic based on astigmatism.

5. The lens of claim 1 , wherein the second freeform optical surface is configured to provide a variable optical output characteristic based on aspheric aberration.

6. 10. The lens of claim 1, wherein the second freeform optical surface is configured to provide a variable optical output characteristic based on any Zernike mode.

7. 10. The lens of claim 1, wherein the second freeform optical surface is configured to provide a variable optical output characteristic based on any combination of a plurality of Zernike modes.

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