Apparatus and method configured for determining choroidal topography over an area on the retina

Abstract

The present invention relates to an apparatus (110) and a method (210) configured to determine a choroidal topography (218) on a region (114, 114') of the retina (116) of a human eye (117), and to the use of the apparatus (110) for determining the effect of at least one ophthalmic lens design on the choroidal topography (218). In this document, the device (110) includes: - at least two separate displays (122, 122'), each configured to provide retinal stimulation (112, 112'), thereby providing two independent retinal stimuli (112, 112'); - at least two optical transmission elements, including a first optical transmission element and a second optical transmission element, each configured to project at least one of the retinal stimulation (112, 112') or a phase map onto a region of the retina of a human eye, wherein the phase map includes a modified retinal stimulation; - a measuring device (142) for capturing a human eye by using reflected light received from a region (114, 114') on the retina (116) of the human eye (117). (117) Choroidal topography (218) on region (114, 114') of retina (116); - Optical filter (152) configured to separate reflected light received from region (114, 114') of retina (116) of human eye (117) from phase map of region (114, 114') of retina (116) of human eye (117), wherein the second optical transmission element is further configured to simultaneously project each of the at least two separate phase maps at different retinal eccentricities onto each of at least two separate regions (134, 134') of retina (116) of human eye (117), wherein these separate regions (134, 134') include peripheral region and foveal region of retina (116) of human eye (117).

Description

Technical Field

[0001] The present invention relates to an apparatus and method configured for determining choroidal topography on a region of the retina of a human eye, and to the use of the apparatus for determining the effect of at least one ophthalmic lens design on choroidal topography. Background Technology

[0002] Current treatments for slowing myopia progression involve wearing ophthalmic lenses designed to increase choroidal thickness, thereby preventing eyeball elongation. Modern lens designs produce different imaging characteristics for the fovea and peripheral retina, as the peripheral retina plays a crucial role in myopia progression. Currently, the effectiveness of these lens designs is evaluated through long-term clinical studies spanning several years, following the provision of lens prototypes.

[0003] The time course of theonset and recovery of axial length changes in response to imposed defocus, by S. Delshad, MJ Collins, SA Read, and SJ Vincent, Scientific Reports, 2020, 10:8322, provides evidence that the human eye can detect and respond to the presence and signs of blur within minutes. As is generally known, the human eye responds to the presence of blur by altering its axial length, causing the retina to move toward the defocused image plane. The authors measured the rate of change of axial length under myopic and hyperopic defocus stimuli, as well as the rate of change of axial length upon removal of defocus. A rapid increase of +7 ± 5 μm was observed in axial length after approximately 2 minutes of exposure to hyperopic defocus, while a slower decrease of -8 ± 9 μm was observed in myopic defocus, which was only statistically significant after 40 minutes. The rate at which axial length recovers to baseline levels during clear vision is faster after hyperopic defocus than after myopic defocus.

[0004] US2016 / 0270656 A1 discloses a configuration of a health system for various healthcare applications, such as for patient diagnosis, monitoring, and / or treatment. This health system may include: a light generation module for transmitting light or images to a user; one or more sensors for detecting physiological parameters of the user's body, including their eyes; and processing circuitry for analyzing input received in response to the presented image to determine one or more health conditions or defects.

[0005] WO 2018 / 165697 A1 discloses a method for measuring the influence of ophthalmic lens design. The method includes: splitting an optical beam into a wavefront detection optical path and a wavefront modulation optical path; implementing the ophthalmic lens design in an adaptive optics device positioned in the wavefront modulation optical path; and obtaining ophthalmic biometric data in the ophthalmic biometric wavefront detection optical path to measure the influence of the ophthalmic lens design. An apparatus and system for measuring the influence of ophthalmic lens design, and a method for assembling the apparatus and system, are also disclosed. The ophthalmic biometric device may be an interferometer, and the adaptive optics device may include one or more wavefront shapers.

[0006] WO 2020 / 102734 A1 discloses systems (e.g., modified fundus camera systems) and methods for measuring ocular anomalies, including: projecting an image of a known target pattern with specific features onto a region of the retinal plane / surface to provide an distorted retinal image of the target pattern on a region of the retinal surface; recording the distorted retinal image of the target pattern using an image sensor to provide a captured distorted retinal image of the target pattern on a region of the retinal surface; identifying specific features of the captured distorted retinal image; and comparing the identified specific features of the captured distorted retinal image of the target pattern on a region of the retinal surface with corresponding specific features of the known target pattern to provide an ocular anomaly map on a region of the retinal surface. Systems and methods for measuring retinal shape are also provided.

[0007] US10,945,597B2 discloses an ophthalmic testing center system based on optical coherence tomography (OCT). The system includes: an OCT scanner comprising an eyepiece for receiving at least one eye of a user or subject; a light source that outputs light directed through the eyepiece into the user's or subject's eye; an interferometer configured to generate optical interference using light reflected from the user's / subject's eye; an optical detector configured to detect the optical interference; and a processing unit coupled to the detector. The ophthalmic testing center system can be configured to perform a large number of self-administered functional and / or structural ophthalmic tests and output test data.

[0008] WO 2021 / 005213 A1 discloses a method, apparatus, and computer program for determining refractive errors in a user's eye. The method for determining refractive errors in a user's eye, wherein the user's eye has a choroid, includes: determining at least one value of the choroidal layer thickness of the user's eye at at least one region of the choroid; and determining values ​​for changes in refractive error of the eye based solely on at least two values ​​of the choroidal layer thickness, each of the at least two values ​​being determined at different times for at least one region of the choroid, wherein the at least one region is selected from the perinasal region or the paranasal region.

[0009] US2021 / 0379399 A1 discloses a stimulus configured to treat astigmatism by altering retinal thickness, either independently of or in conjunction with a myopia treatment process. In some embodiments, the stimulus pattern is arranged relative to the astigmatic axis of the eye to reduce axial elongation relative to the astigmatic axis. In some embodiments, the device is configured to direct light relative to the astigmatic axis of the eye to a retinal region outside the macula. In some embodiments, the intensity is modulated to achieve the effect. Lenses (such as contact lenses or spectacle lenses) may be configured to have multiple light sources, such as a projection unit with light sources and focusing optics, which work together to project a forward-defocused or backward-defocused image onto the retina at an off-center foveal location.

[0010] US2020 / 081269 A1 discloses a method for measuring the impact of ophthalmic lens design. The method includes: splitting an optical beam into a wavefront detection path and a wavefront modulation path; implementing the ophthalmic lens design in an adaptive optics device positioned in the wavefront modulation path; and obtaining ophthalmic biometric data in the ophthalmic biometric wavefront detection path to measure the impact of the ophthalmic lens design. An apparatus and system for measuring the impact of ophthalmic lens design, and a method for assembling the apparatus and system, are also disclosed. The ophthalmic biometric device may be an interferometer, and the adaptive optics device may include one or more wavefront shapers.

[0011] WO 2021 / 259982 A1 discloses an apparatus and method for determining the ocular aberration of at least one eye of a user. The apparatus includes: a wavefront sensing unit designated for measuring at least one optical wavefront composed of at least one light beam, wherein the ocular aberration of at least one eye of the user is determined based on the at least one optical wavefront; and at least one diffractive element for generating multiple diffraction orders in two meridional planes within the at least one light beam, such that these multiple diffraction orders are spatially separated on the wavefront sensing unit and in the at least one eye of the user.

[0012] The problem to be solved

[0013] In particular, regarding the disclosure in US2020 / 081269 A1, the object of the present invention is to provide an apparatus and method configured for determining choroidal topography on a region of the retina of a human eye, and the use of the apparatus for determining the effect of at least one ophthalmic lens design on the choroidal topography, which at least partially overcomes the limitations of the prior art.

[0014] A specific object of the present invention is to provide an apparatus and method configured to determine short-term temporal changes in the choroid due to ophthalmic lens design. Furthermore, it is desirable that the apparatus and method can be further configured to reproduce the performance of the ophthalmic lens design for foveal and peripheral vision, and to determine choroidal topography under short-term (preferably within a few minutes) retinal stimulation. The short-term results obtained in this way can be used to predict long-term effects, thus allowing for the optimization of ophthalmic lens designs prior to clinical studies. Summary of the Invention

[0015] This problem is addressed by an apparatus and method, having the features of the independent claims, configured to determine choroidal topography over a region of the retina of a human eye, and the use of the apparatus to determine the effect of at least one ophthalmic lens design on the choroidal topography. Preferred embodiments that can be implemented individually or in any combination are set forth in the dependent claims and throughout the following description.

[0016] In a first aspect, the present invention relates to an apparatus configured for determining a choroidal topography over a region on the retina of a human eye. Hereinafter, the apparatus includes:

[0017] - At least two separate displays, each configured to provide retinal stimulation, thereby providing two independent retinal stimuli;

[0018] - At least two optical transmission elements, including a first optical transmission element and a second optical transmission element, each of the at least two optical transmission elements being configured to project at least one of a retinal stimulus or a phase map onto a region of the retina of a human eye, wherein the phase map includes a modified retinal stimulus;

[0019] - A measuring device for capturing choroidal topography on a region of the retina of a human eye by using reflected light received from a region on the retina of the human eye.

[0020] - An optical filter configured to separate reflected light received from a region on the retina of the human eye from the phase map projected onto that region on the retina.

[0021] The second optical transmission element is further configured to simultaneously project each of at least two separate phase maps onto each of at least two separate regions on the retina of a human eye with different retinal eccentricities, wherein these separate regions include a peripheral region and a foveal region on the retina of a human eye.

[0022] As commonly used, the term "device" refers to a device having at least two elements that operate in a manner that achieves the desired purpose of the device. In this document, the device is configured to project retinal stimulation onto an area of ​​the retina of a human eye and / or to determine choroidal topography on an area of ​​the retina of a human eye. For this purpose, the at least two elements of the device may preferably be constituted by a single device; however, in other embodiments, these elements may be distributed in different locations, wherein at least one communication element (e.g., at least one of a light beam, a physical optical component, or an electronic component) may be used for communication between the locally separated elements.

[0023] According to the invention, the device may include a first module and a second module, as described in more detail below, which communicate with each other in such a manner; however, different arrangements are also contemplated. As used herein, the term "module" refers to a specific element of the device, as described in more detail below. Hereinafter, the terms "first" and "second" are considered descriptions of specific elements without specifying an order or chronological sequence, and do not exclude the possibility of other elements of the same type. In a particularly preferred embodiment, the first module may include at least two optical transmission elements and at least one digitally addressed optical modulation element, while the second module may include a measuring device and an optical filter; however, different arrangements may also be feasible.

[0024] As described above, the device includes at least two optical transmission elements configured to project retinal stimulation and / or a phase map onto a region of the retina of a human eye. As commonly used, the term "projection" or any grammatical variation thereof refers to the process of displaying a light sheet onto an object, in this context, the retina of a human eye. Different terms may be used besides "human," such as "subject," "user," "tester," or "glasses wearer." As commonly used, the term "retina" or any grammatical variation thereof refers to a photosensitive tissue layer in the human eye configured to record an image produced by incident light. In this document, the lateral extent of the retina may exceed the retinal thickness by at least 10 times, preferably 20 times, and particularly preferably 50 times. As further used herein, the term "optical transmission element" refers to an optical element configured to modify at least one characteristic of incident light, wherein the at least one characteristic may be particularly selected from at least one of the propagation direction, bandwidth, wavelength, or color of the light included in the light sheet. Typically, the at least one optical element can be specifically selected from relay lenses, mirrors, cold mirrors, prisms, beam splitters, rotating beam splitters, or diffractive elements (such as gratings). Unlike digitally addressed optical modulation elements, particularly spatial optical modulators described in more detail below, optical transmission elements as used herein are not configured to change the phase of light.

[0025] In a preferred embodiment, the device may include a first optical transmission element and a second transmission element, wherein the second optical transmission element may be further configured to simultaneously project each of at least two separate phase maps onto each of at least two separate regions on the retina of a human eye with different retinal eccentricities. In this way, the second optical transmission element is capable of simultaneously measuring in both the foveal and peripheral regions, which is not possible according to known prior art. A third optical transmission element may be further employed when using a single digitally addressed optical modulation element as described in detail below.

[0026] For the purpose of generating a phase map, the device may particularly preferably include at least one digitally addressed optical modulation element. As used herein, the term “generate” or any grammatical deviation thereof refers to the process of generating a phase map. As commonly used, the term “map” refers to a two-dimensional representation of an object. Thus, the term “phase map” refers to a two-dimensional representation of local values ​​of the phase describing at least one characteristic of an optical sheet, wherein the at least one characteristic may particularly be selected from at least one of the intensity, polarization, or color of the light included in the optical sheet. As used herein, the term “light” refers to electromagnetic radiation selected from at least one of visible light or infrared (IR) light. As commonly used, the term “visible light” refers to electromagnetic radiation with wavelengths from 380 nm to 780 nm, while the terms “infrared light” and “IR light” refer to electromagnetic radiation with wavelengths above 780 nm to about 1000 μm, wherein near-IR light with wavelengths above 780 nm to about 1.5 μm may be particularly preferred.

[0027] As further used herein, the term "digitally addressed optical modulator" refers to an optical device having a plurality of individually controllable optical elements designed for modulating an incident light beam. A digitally addressed optical modulator can be specifically configured to generate at least one phase map that modulates at least one image characteristic of each of a retinal stimulus. Preferably, the digitally addressed optical modulator can be selected from spatial light modulators or digital micromirror devices. As commonly used, the term "spatial light modulator" or "SLM" refers to an optical device configured to electronically and / or optically imprint an intensity pattern or phase pattern onto an incident light beam. Further, the term "digital micromirror device" or "DMD" refers to an optical device configured to modulate a digital image onto a light beam. For this purpose, a digital micromirror device includes a plurality of tilted micromirrors having edge lengths in the micrometer range and arranged in a matrix, each micromirror being individually addressable using an electrostatic field. In this way, the incident light beam can be split into individual pixels and subsequently reflected pixel by pixel. However, it is also feasible to use other types of digitally addressed optical modulators.

[0028] Accordingly, digitally addressed optical modulation elements can be configured to generate a phase map by modifying at least one imaging characteristic of a retinal stimulus. As used herein, the term “modify” or any grammatical variation thereof refers to the process of altering at least one characteristic of an object. In this document, at least one imaging characteristic of a retinal stimulus is altered by using a digitally addressed optical modulation element, thereby generating a desired phase map. As further used herein, the term “retinal stimulus” refers to a graphic representation of a visual stimulus that is known or reasonably expected by those skilled in the art to be suitable for evoking a response in the retina of the human eye. A retinal stimulus may be particularly suitable if it is perceptible to a human, in particular, due to the contrast between the retinal stimulus and the background, which allows the human eye to distinguish between the retinal stimulus and the background. In this document, a retinal stimulus is represented in such a way that the response of the human eye’s retina includes the difference between reflected light received from an area on the retina of the human eye and the phase map projected onto the area on the retina of the human eye.

[0029] According to the invention, the device can be configured to generate at least two separate phase maps. As used herein, the term "separate" refers to a specific object among a plurality of objects, wherein each object can be distinguished from the others by at least one characteristic, thereby generating mutually distinguishable objects. For the purposes of the invention, at least two separate phase maps can be distinguished from each other, particularly by including at least one element that can distinguish them from other phase maps, wherein the at least one element can be selected from at least one of the intensity, phase, polarization, or color of the light included in the light sheet, which constitutes a separate phase map as defined above.

[0030] According to the present invention, at least one single digitally addressed optical modulation element can be used. In one embodiment, at least two digitally addressed optical modulation elements can be used to generate at least two phase maps from at least two retinal stimuli. In other words, each digitally addressed optical modulation element is assigned to each retinal stimulus and generates a corresponding phase map. That is, more than one single digitally addressed optical modulation element is used only when it is desired to generate at least two phase maps simultaneously from at least two retinal stimuli. For devices not configured to project at least two phase maps onto the retina simultaneously, more than one single digitally addressed optical modulation element is not necessarily required. In embodiments, more than one single digitally addressed optical modulation element can be used to cause axial variation only with different wavelengths, especially since the performance of a single digitally addressed optical modulation element is generally wavelength-dependent, and accurate generation of phase maps at different wavelengths may require different single digitally addressed optical modulation elements with optimized performance at each wavelength.

[0031] In one embodiment, the device may include a single digitally addressed optical modulation element configured to generate at least two of these individual phase maps, particularly in parallel. Further, the device may preferably include a third optical transmission element and a second optical transmission element configured to provide at least two individual retinal stimuli to the single digitally addressed optical modulation element. The second optical transmission element may be further configured to simultaneously project each of the at least two individual phase maps onto each of at least two individual regions on the retina with different retinal eccentricities. The second optical transmission element is further configured to separate the at least two individual phase maps before projecting them onto one of the at least two individual regions on the retina of the human eye. In one embodiment, the third and second optical transmission elements may include at least two mirrors or at least two optical lenses (preferably selected from at least two single lenses or multi-lens arrays) and at least one prism; however, different configurations of the optical transmission elements are also feasible, as long as the optical transmission elements are capable of simultaneously projecting at least two different phase maps onto at least two different regions on the retina with different eccentricities.

[0032] This device may further include a light path diverter. As commonly used, the term "light path diverter" refers to an optical transmission element configured to guide a light path around an object. A light path diverter can combine the paths of light beams from different modules and project them onto at least two separate regions of the retina of a human eye. In particular, a light path diverter can be used to achieve pupillary plane conjugation by replicating the phase and amplitude of at least one wavefront at different locations. In one embodiment, a light path diverter may include at least two parabolic mirrors or at least two achromatic lenses. The use of such a light path diverter differs in particular from US2020 / 0081269A1, as a light path diverter in front of the ocular biometry device is not required because only a single location on the retina is stimulated and measured during a single measurement, and it is not intended to simultaneously stimulate the foveal region and the peripheral retinal region. According to the invention, two-dimensional fundus tomography is used by employing at least one light path diverter in a second module. In another embodiment, at least one light path diverter may be used only in a single module. In an alternative embodiment, both the first and second modules may share components of the light path diverter in front of the eye.

[0033] Ocular aberrations depend on illumination eccentricity and result in only a limited area of ​​the retina having uniform image characteristics. This area is also called the "isohalo zone" and is typically about 1°. Therefore, when a single stimulus greater than 1° is projected onto the retina, the programmed image characteristics can only be accurately reproduced within a disc-shaped area of ​​about 1°. Within this disc-shaped area, the image characteristics of the stimulus may vary unpredictably, leading to increased variability in measurements and reduced reliability of results. Furthermore, accurately replicating this type of simultaneous stimulation while preserving programmed image characteristics cannot be achieved by projecting a single beam into the eye. Furthermore, it should be noted that natural temporal variations in the choroid (e.g., caused by circadian rhythms) may reduce the reliability of conclusions drawn from stimuli administered at different times. In contrast, the device according to the invention is capable of simultaneously measuring at least two different regions by providing at least two stimuli from at least two separate displays and using at least one optical transmission element and at least one optical path deflector, the at least one optical transmission element being configured to simultaneously project each of at least two separate phase maps with different retinal eccentricities onto each of at least two separate regions on the retina.

[0034] In another embodiment, the polychromatic retinal stimuli have independent image characteristics at at least two different wavelengths, and these polychromatic retinal stimuli can be projected onto one of at least two separate regions of the retina of the human eye. For this purpose, the polychromatic retinal stimuli can preferably be generated using one or more laser devices (e.g., laser diodes) and combined via time multiplexing, wherein at least one display can be configured to emit retinal stimuli for at least two selected wavelengths. A combination of optical elements (e.g., trichromatic prisms) and optical filters (particularly variable filters) can be used to direct corresponding portions of a monochromatic beam to at least one display and a synchronization device configured to drive a time sequence of monochromatic illumination for each selected wavelength, wherein the synchronization device can be further configured to trigger at least one display and address at least one digitally addressable optical modulation element to project an intensity map and a corresponding phase map of the polychromatic retinal stimuli, the phase map being configured to modify the image characteristics of the polychromatic retinal stimuli for each selected wavelength. The wavelength dependence of the performance of the at least one digitally addressable optical modulation element can be adjusted by projecting an optimized phase map onto each wavelength after calibrating the phase modulation of the digitally addressable optical modulation element for each selected wavelength.

[0035] In another embodiment, the optical modulation element included in the device may be a separate digitally addressed optical modulation element configured to generate one of at least two separate phase maps. Hereinafter, a separate display may be configured to provide a single retinal stimulus to the corresponding separate digitally addressed optical modulation element. For this purpose, the device further includes at least two separate displays, each of which may be configured to provide at least one (preferably one) separate retinal stimulus, wherein at least one of the imaging characteristics of each retinal stimulus can be modified by generating each separate phase map using the digitally addressed optical modulation element. In a preferred embodiment, the separate display provides a single retinal stimulus. As used herein, the term "display" refers to an electronic device designed to present at least one separate retinal stimulus. In particular, at least one display may be a screen or monitor, especially including liquid crystals or digital micromirrors configured to present at least one separate retinal stimulus to a separate digitally addressed optical modulation element. Further, the term "separate display" herein refers to a complete device as a whole, and does not include a separate screen on a single display (e.g., a microdisplay) displaying multiple different retinal stimuli. This is because a single display that shows several stimuli would require additional optics and complex configuration.

[0036] In this embodiment, the device may therefore include at least two optical modulation elements, particularly multiple digitally addressed optical modulation elements, especially at least two spatial light modulators, or at least two digital micromirror devices. Hereinafter, these two optical modulation elements may preferably be oriented to generate multiple retinal stimuli with independent image characteristics. This feature contrasts with US2020 / 081269A1, which only discloses that the purpose of having multiple spatial light modulators is to induce axial variations with different wavelengths. This is based on the observation that the performance of spatial light modulators depends on the wavelength, and therefore, accurately implementing phase maps for different wavelengths requires different spatial light modulators with optimized performance at the corresponding wavelengths.

[0037] As described above, according to the invention, the device is configured to project each of at least two separate phase maps onto one of at least two separate regions on the retina of a human eye. In this context, at least one of these separate regions is a peripheral region on the retina of a human eye, extending beyond the fovea of ​​the retina. As commonly used, the term "fovea" refers to a small central region on the retina of a human eye designated for clear central vision. As used herein, the term "separate region" refers to a separate region on the retina, wherein the two separate regions are distinguished by corresponding regions on which separate phase maps are projected. Particularly preferred, the two separate regions do not overlap. For example, a first separate phase map is projected onto the central region of the retina including the fovea, while a second separate phase map is also projected onto the retina of a human eye, but onto a peripheral region excluding the fovea.

[0038] To generate a first separate phase map to be projected onto the central region of the retina, including the fovea, at least one central retinal stimulus may be used, preferably selected from at least one of the following:

[0039] - A static image of the object;

[0040] -Movie;

[0041] -Spatial regular patterns,

[0042] The image, film, or pattern may be monochrome or color. In contrast, at least one peripheral retinal stimulus may be used to generate a second, separate phase image to be projected onto a peripheral region excluding the fovea, wherein the at least one peripheral retinal stimulus may preferably be selected from at least one of the following:

[0043] -Spatial regular patterns;

[0044] - A static image of the object;

[0045] -Movie,

[0046] The pattern, image, or film can be monochrome or color. However, it may be feasible to use another type of central or peripheral retinal stimulation.

[0047] In a particularly preferred embodiment, the second optical transmission element can be configured to simultaneously project each individual phase map onto more than one region of at least two separate regions on the retina of the human eye with different retinal eccentricities. As commonly used, the term "simultaneously" means performing two processes in such a way that at least a portion of the two processes is performed within the same time interval. In particular, at least one optical transmission element can be configured to project each individual phase map onto each separate region of the retina of the human eye with different retinal eccentricities. As commonly used, the term "retinal eccentricity" refers to the angle between two beams, each beam comprising a separate phase map to be projected onto the retina as a sheet. In a particular embodiment, at least one optical transmission element can be configured to project at least one of at least two individual phase maps with a fixed retinal eccentricity. Such an optical transmission element is not required in prior art devices that do not assume simultaneous measurements in the foveal and peripheral regions.

[0048] As commonly used, the term "fixed" refers to a constant value that does not change during a predefined time interval. In a preferred alternative embodiment, at least one optical transmission element may be configured to project at least one of at least two separate phase maps with a variable eccentricity. As commonly used, the term "variable" refers to a value that changes during a predefined time interval. In this alternative embodiment, a second optical transmission element is configured to simultaneously project each of at least two separate phase maps with different retinal eccentricities onto each of at least two separate regions on the retina. Hereinafter, the second optical transmission element may be or includes a rotating beam splitter (RBS) configured to project at least one beam onto the retina of a human eye with a specific eccentricity. As commonly used, the term "beam splitter" refers to a specific type of optical element used to split a beam into at least two (particularly exactly two) partial beams. Hereinafter, beam splitters may generally be selected from any known beam splitter, particularly from glass plates or cubes with dielectric coatings, dichroic mirrors, protective film beam splitters, or polarizing beam splitters (such as Wollaston prisms or polarizing gratings). However, it is also feasible to use different types of optical transmission elements.

[0049] In an alternative embodiment, described in more detail below, the device may further include at least one refractive correction element, which may preferably be a non-pixelated correction element. This at least one refractive correction element may be configured to generate one of at least two separate phase maps. As used herein, the terms "refractive correction element" or "non-pixelated correction element" refer to an optical element with predefined visual correction (particularly indicated by ± diopter). Typically, the field of view (FOV) of pixelated digitally addressed optical modulation elements (such as spatial light modulators) is limited, particularly because millions of pixels arranged in a rectangular or square configuration may create copies of the image seen through these pixels, which may overlap as the number of image copies increases. Therefore, in the prior art, the use of pixelated digitally addressed optical modulation elements is considered unsuitable for generating phase maps of wide field of view (FOV) stimuli. In contrast, in this document, non-pixelated correction elements are used to generate phase maps of wide FOV stimuli. Preferably, at least one refractive correction element (especially at least one non-pixelated correction element) can be at least one deformable mirror, a single optical lens, or a group of optical lenses, preferably at least one solid optical lens or at least one tunable liquid lens; however, it is also feasible to use different types of optical elements.

[0050] As indicated above, the device further includes a measuring device configured to capture a choroidal topography over an area on the retina of the human eye. As commonly used, the terms "choroid" and "of the choroid" refer to an intermediate layer disposed on the side of the eye away from light incidence, between the sclera and the retina, particularly between the sclera and the retinal pigment epithelium. This type of arrangement of the choroid in the eye presents the following: the thickness of the choroidal layer is defined by the adjacent sclera and retina, particularly the sclera and the retinal pigment epithelium. Within the scope of this invention, the term "choroidal layer thickness" refers to the distance between the sclera and the retina, which is determined substantially perpendicular to the lateral extension direction of the choroid. Hereinafter, the lateral extension of the choroid may exceed the choroidal layer thickness by at least 10, preferably at least 20, and particularly preferably at least 50 times.

[0051] As used further herein, the term "capture" or any grammatical variation thereof refers to a record from which a choroidal topography, particularly the choroidal layer thickness, can be derived by measuring at least one captured variable. In relation to the invention, capturing a choroidal topography on an area of ​​the retina of the human eye involves using reflected light received from that area of ​​the retina. For this purpose, the use of an optical method is particularly preferred. The term "optical method" refers to the process by which light (preferably from the visible or infrared spectral range) is irradiated onto an area of ​​the retina of the human eye, whereby the reflection of light from this area allows conclusions to be drawn regarding the choroidal topography, particularly the choroidal layer thickness. Alternatively or additionally, acoustic or photoacoustic methods may also be used. Hereinafter, the terms "acoustic method" or "photoacoustic method" refer to the process by which the retina is struck by sound waves, preferably ultrasound waves, wherein the measuring device is configured to capture the sound waves, preferably ultrasound waves, acoustically or optically, respectively.

[0052] In a particularly preferred configuration, the optical method may be selected from methods used for optical coherence tomography (OCT). For this purpose, the measuring device for capturing a choroidal topography map of a region on the retina of the human eye may be or includes an optical coherence tomography (OCT) system. As commonly used, the terms "optical coherence tomography" and "OCT" refer to imaging methods for generating two-dimensional or three-dimensional records of biological tissue, particularly the choroid, wherein resolution in the micrometer range can preferably be obtained. To generate the desired record, light with a short temporal coherence length from a radiation source is split into two parts in a beamsplitter, wherein a first part of the light is incident on the tissue along the optical axis, wherein a second part of the light is guided on a reference path, and wherein the light reflected from the tissue interferes with the reference light guided on the reference path to generate an interference signal. Based on the interference signal generated thereby, structures in tissue (especially those on the retina of the human eye) can initially be distinguished only along the optical axis; however, a desired two-dimensional or three-dimensional record of the tissue or a portion thereof can be generated using a scanning device configured to alter the direction of the optical axis in the tissue, in other words, to change the eccentricity of light passing through the pupil of the human eye, particularly the direction of the optical axis relative to the retina of the human eye. Preferably, the scanning device can be configured to alter the direction of the optical axis and interrogate different regions of the retina of the human eye.

[0053] Preferably, the optical coherence tomography method can be selected from Fourier domain OCT or time-domain OCT, wherein Fourier domain OCT, particularly spectral domain OCT or swept-source OCT, is particularly preferred. The term "time-domain OCT" refers to the process of changing the length of the reference path and continuously capturing the intensity of the interference during the process, without considering changes in the interference spectrum. Further, the term "Fourier domain OCT" refers to a process that takes into account changes in the components of the interference spectrum. If changes in the interference spectrum are simultaneously excited and captured by a broadband radiation source, this process is typically called "spectral domain OCT." Furthermore, in "swept-source OCT," the components of the spectrum are successively excited and captured in time, particularly by successively tuning the frequency excitation of the radiation source.

[0054] In alternative embodiments, the optical method may be selected from adaptive optics methods. As commonly used, the term "adaptive optics method" refers to a process configured to detect, manipulate, and compensate for optical deviations in at least one of a measuring device or an eye. By using adaptive optics methods, the influence of at least one of the measuring device, eye, or programmed imaging characteristics on changes detected in choroidal topography can be addressed. Preferably, the adaptive optics method may involve combined operation of at least one eye aberration meter and at least one digitally addressed optical modulation element. However, the use of other types of adaptive optics methods and apparatus is also conceivable.

[0055] In a preferred embodiment, the device may further include at least one optical relay system configured to provide at least one individual retinal stimulus to a corresponding individual digitally addressed optical modulation element. As commonly used, the term "optical relay system" refers to a combination of at least two optical elements designated for transmitting an optical plane to different locations. For example, the retinal stimulus shown on the display could thus be transmitted to the inlet of the optical modulation element, or a separate phase map positioned at the outlet of the optical modulation element could thus be transmitted for display on the pupil of a human eye. Preferably, the relay optical system may include at least one of a parabolic mirror or an optical lens; however, the use of at least one additional optical element may also be feasible.

[0056] In another preferred embodiment, the first device may additionally include at least one Badal stage, which can be configured to correct defocus errors. Particularly preferred, at least one Badal stage may be incorporated into at least one optical relay system. As commonly used, the term "Badal lens" refers to an optical element comprising at least one lens configured to display a target at the same angular size. In this other preferred embodiment, the Badal lens can advantageously be used to correct spherical errors.

[0057] In yet another preferred embodiment, the first device may additionally include at least one aberration meter, which may be configured to determine at least one value of ocular aberration at at least two separate regions on the retina of a human eye using reflected light received from a region on the retina of the human eye. In particular, the at least one aberration meter may be specifically configured to determine at least one value of refractive effect associated with at least two separate regions on the retina of the human eye. As commonly used, the term “ocular aberration” refers to the difference between the surface of an ideal optical wavefront determined for at least one human eye and the surface of an actual optical wavefront. Hereinafter, the term “optical wavefront” refers to a surface perpendicular to the beam of light along which it propagates. In a typical human population, ocular aberration typically includes at least one second-order cylindrical focusing error, also known as “refractive effect”; however, at least one higher-order aberration may also occur. As further commonly used, the term “ocular aberration meter” refers to means configured to determine at least one value of the difference between the surface of an ideal optical wavefront and the surface of an actual optical wavefront in a process typically referred to by the term “ocular aberration measurement.” For the purpose of determining at least one value of the refractive effect, the first device may specifically include a separate aberration meter for each different degree of retinal eccentricity. In an alternative embodiment, the device may include only a single aberration meter for at least two different degrees of retinal eccentricity.

[0058] In a particular embodiment, at least one eye aberration meter may preferably be or include at least one wavefront sensor. As commonly used, the term "wavefront sensor" refers to an optical sensor for measuring aberrations of an optical wavefront, wherein the term is generally applicable to optical sensors that do not require interference with a reference beam that does not have aberrations. In this document, the wavefront sensor may preferably be selected from at least one of the following: a Hartmann-Shack wavefront sensor (HSWS), a camera for measuring at least one point spread function of an eccentric wavefront, a circular microlens array aberration meter, a pyramid wavefront sensor, a phase element-based wavefront sensor, and a ray-tracing aberration meter. However, other types of wavefront sensors may also be feasible. As commonly used, the terms "Hartmann-Shack wavefront sensor" and "HSWS" refer to a particular type of wavefront sensor comprising an array of individual microlenses (which are generally referred to by the term "microlenses") and a two-dimensional optical detector (such as a CCD array, CMOS array, or quaternion), wherein, when uniformly illuminated by the microlenses, the integral gradient of the incident optical wavefront on each microlens is proportional to the displacement produced by each individual microlens. In other words, the phase aberration of the incident optical wavefront can therefore be approximated by a set of local tilts corresponding to these individual microlenses, where the tilts corresponding to these microlenses can also be expressed by the term "eccentricity". By sampling the incident optical wavefront in this way by means of an array of microlenses, the incident optical wavefront can therefore be at least partially, and preferably completely, reconstructed by measuring the local eccentricity of each individual microlens within the array of microlenses.

[0059] In another preferred embodiment, the device may additionally include at least one light source configured to generate at least one light beam for determining at least one value of ocular aberration. As commonly used, the term "light source" refers to a means for generating at least one light beam, wherein at least one light beam provided by the light source is guided along at least one optical path. In this document, the at least one light source may preferably generate light with a wavelength longer than that used in measuring devices, particularly for optical coherence tomography systems, and therefore may be or include an IR light source, particularly an IR light-emitting diode. As mentioned above, IR light refers to electromagnetic radiation with wavelengths above 780 nm to about 1000 μm, wherein near-IR light with wavelengths above 780 nm to about 1.5 μm may be particularly preferred. In particular, at least one ocular aberrometer may be configured to determine at least one value of ocular aberration at at least two separate areas on the retina of a human eye, in a manner particularly using a portion of reflected light received from areas on the retina of a human eye, which has been generated by using at least one light source.

[0060] In yet another preferred embodiment, the device may further include at least two polarizers configured to suppress specular reflections on the cornea of ​​the human eye. These at least two polarizers may be placed adjacent to each other in the beam path, wherein each polarizer is configured to allow a portion of the wavefront with a specific polarization to pass through while blocking another portion of the wavefront with a different polarization. Specifically, the at least two polarizers may be placed in front of at least one of an aberrometer (particularly a Hartmann-Shack wavefront sensor (HSWS)) and a light source (preferably an IR light source, particularly an IR light-emitting diode). In this way, the processing of the aberrometer, particularly the Hartmann-Shack wavefront sensor (HSWS), can be improved by suppressing specular reflections on the cornea.

[0061] In yet another preferred embodiment, the device may additionally include at least one camera configured to determine the alignment of a person's eyes. As commonly used, the term "camera" refers to means configured to generate at least one image of an object. As used herein, the term "alignment" refers to the relative orientation of a person's eyes. For the purpose of ensuring high-quality measurements, particularly during the projection of a phase map onto an area of ​​the retina of a person's eye and the capture of choroidal topography on that area, the pupils of the person's eyes can be monitored using at least one camera, preferably two cameras, and IR light-emitting diodes invisible to the human eye.

[0062] As indicated above, the device further includes an optical filter configured to separate reflected light received from a region on the retina of the human eye from a phase map projected onto the region on the retina of the human eye. As commonly used, the term "optical filter" refers to an optical element configured to selectively allow at least a portion of incident light to pass through in at least one direction. Preferably, the optical filter may be selected from at least one of a dichroic mirror, a spectral filter, or a beam splitter; however, it is also feasible to use different types of optical filters. As commonly used, the term "dichroic mirror" is configured to selectively allow incident light having a small wavelength range to pass through and reflect incident light outside the small wavelength range.

[0063] In a particularly preferred embodiment, the device may further include a processing means, which may be configured to both control at least one element (preferably a module) of the device and determine the effect of at least one ophthalmic lens design on choroidal topography. As commonly used, the term "processing" or any syntactic variation thereof refers to applying at least one algorithm to input data to determine output data. As commonly used, the term "determine" or any syntactic variation thereof refers to the process of interpreting input data, specifically to obtain at least one representative result. According to the invention, input data including values ​​of choroidal topography can be used for the purpose of determining the effect of at least one ophthalmic lens design on choroidal topography. Other uses of the processing means may be feasible.

[0064] In another aspect, the present invention relates to a method configured for determining a choroidal topography map of a region on the retina of a human eye. The method includes steps a) through c):

[0065] a) Projecting a phase map onto a region of the retina of a human eye using at least one optical transmission element, wherein the phase map includes a modified retinal stimulus;

[0066] b) Separating the reflected light received from the region on the retina of the human eye from the phase map projected onto the region on the retina of the human eye using an optical filter; and

[0067] c) Capturing choroidal topography on a region of the retina of a human eye by using a measuring device to determine the reflected light received from that region; and

[0068] By using at least two separate displays to provide at least two independent retinal stimuli, and simultaneously projecting each of the at least two separate phase maps with different retinal eccentricities onto each of at least two separate regions on the retina of a human eye, wherein the at least two separate regions include the peripheral region and the foveal region on the retina of a human eye.

[0069] In this document, the indicated steps can preferably be performed in a given order, starting with step a), continuing with step b), and ending with step c). However, any indicated step, or all indicated steps, can also be performed partially simultaneously and / or repeated several times. Further, as particularly preferred, the steps of this method can be performed using devices as described elsewhere herein.

[0070] According to step a), at least two separate phase maps are projected onto at least two separate regions on the retina of a human eye, wherein at least one of these two separate regions is a peripheral region on the retina of the human eye, extending beyond the fovea of ​​the retina. For this purpose, preferably, at least one optical transmission element as described in more detail above or below can be used. In a particularly preferred embodiment, each separate phase map can be simultaneously projected onto more than one of the at least two separate regions on the retina of the human eye.

[0071] According to step b), the reflected light received from the region on the retina of the human eye is separated from the phase map projected onto the region on the retina of the human eye.

[0072] According to step c), a choroidal topography map is captured on an area of ​​the retina of the human eye. For this purpose, preferably, the reflected light received from the area of ​​the retina of the human eye can be used by a measuring device as described in more detail above or below.

[0073] In a preferred embodiment, the method may further include at least one of the following steps:

[0074] d) By using a digitally addressed optical modulation element, at least one phase map among these individual phase maps is generated by modifying at least one imaging characteristic of the retinal stimulus;

[0075] e) By using at least one ocular aberration meter, at least one value of ocular aberration at at least two separate areas of the retina of a human eye is determined using reflected light received from a region on the retina of the human eye.

[0076] f) Generate at least one light beam used in determining at least one value of eye aberration by using at least one light source;

[0077] g) Determine the alignment of a person's eyes by using at least one camera.

[0078] For further details regarding the method for projecting retinal stimulation onto a region of the retina of a human eye and for determining choroidal topography on that region of the retina, refer to the description of the apparatus for projecting retinal stimulation onto a region of the retina of a human eye and for determining choroidal topography on that region of the retina, provided elsewhere in this document.

[0079] In another aspect, the present invention relates to the use of an apparatus, as described in more detail above or below, for determining the effect of at least one ophthalmic lens design on choroidal topography. As commonly used, the term "ophthalmic lens design" refers to a procedure designed to generate a set of parameters for use in the manufacture of at least one spectacle lens for human use.

[0080] Therefore, in particular, the device and corresponding method can be used to determine short-term temporal changes in choroidal topography caused by at least one ophthalmic lens design. Further, advantageously, the device and corresponding method can be used to reproduce the performance of the ophthalmic lens design for foveal and peripheral vision, and to determine choroidal topography under short-term (preferably within a few minutes) retinal stimulation. Thus, the short-term results obtained in this way can be used to predict long-term effects, thereby allowing for the optimization of ophthalmic lens designs prior to clinical studies.

[0081] As used herein, the terms “have,” “include,” or “include,” or any grammatical variations thereof, are used in a non-exclusive manner. Thus, these terms can refer either to a situation where no other features exist in the entity described in this context besides those introduced by these terms, or to a situation where one or more other features exist. For example, the statements “A has B,” “A includes B,” and “A includes B” can all refer to a situation where no other elements exist in A besides B (i.e., A is solely and exclusively composed of B), or to a situation where entity A contains one or more other elements besides B, such as element C, element C and element D, or even other elements.

[0082] As further used herein, the terms “preferredly,” “more preferably,” “particularly,” “even more particularly,” or similar terms are used in combination with optional features without limiting the possibility of alternatives. Therefore, features described by these terms are optional features and are not intended to limit the scope of the claims in any way. As those skilled in the art will recognize, the invention can be practiced by using alternative features. Similarly, features described by “in embodiments of the invention” or similar expressions are intended to be optional features, without any limitation on alternative embodiments of the invention, without any limitation on the scope of the invention, and without any limitation on the possibility of combining features described in this way with other features of the invention.

[0083] In summary, the following embodiments are particularly preferred within the scope of the present invention:

[0084] Example 1. An apparatus for projecting retinal stimulation onto a region of the retina of a human eye and for determining choroidal topography on a region of the retina of a human eye, the apparatus comprising:

[0085] - At least one optical transmission element configured to project a phase map onto a region of the retina of a human eye, wherein the phase map includes a modified retinal stimulus;

[0086] - A measuring device for capturing choroidal topography on a region of the retina of a human eye by using reflected light received from a region on the retina of the human eye.

[0087] - An optical filter configured to separate reflected light received from a region on the retina of the human eye from the phase map projected onto that region on the retina.

[0088] The device is configured to generate at least two separate phase maps, wherein the at least one optical transmission element is configured to project each separate phase map onto one of at least two separate regions on the retina of a human eye, wherein at least one of the two separate regions is a peripheral region on the retina of a human eye, extending beyond the fovea on the retina of a human eye.

[0089] Example 2. The device according to the previous embodiment, wherein the at least one optical transmission element is configured to simultaneously project each individual phase map onto more than one region in at least two individual regions on the retina of a human eye.

[0090] Example 3. The device according to any of the foregoing embodiments, wherein the at least one optical transmission element is configured to project each individual phase map onto each individual region of the retina of a human eye with different retinal eccentricities.

[0091] Example 4. The device according to the previous embodiment, wherein the at least one optical transmission element is configured to project at least one of the at least two separate phase maps with a fixed retinal eccentricity.

[0092] Example 5. The device according to any of the first two examples, wherein the at least one optical transmission element is configured to project at least one of the at least two separate phase maps with a variable eccentricity.

[0093] Example 6. The device according to the previous embodiment, wherein the at least one optical transmission element is or includes at least one of a mirror, a beam splitter, a rotating beam splitter, or a diffractive element, configured to project at least one light beam onto the retina of a human eye with a specific eccentricity.

[0094] Example 7. The device according to any of the foregoing embodiments, wherein the optical filter is selected from at least one of a dichroic mirror, a spectral filter, a beam splitter, or a rotating beam splitter.

[0095] Example 8. The device according to any of the foregoing embodiments further includes:

[0096] - At least one digitally addressed optical modulation element configured to generate the at least two separate phase maps by modifying at least one imaging characteristic of the at least two retinal stimuli.

[0097] Example 9. The device according to the previous embodiment, wherein the digitally addressed optical modulation element is or includes at least one spatial optical modulator (SLM) or digital micromirror device (DMD).

[0098] Example 10. The device according to any one of the preceding two examples further includes:

[0099] - A single digitally addressed optical modulation element configured to generate at least two phase maps from these individual phase maps.

[0100] - A first optical path diverter, configured to provide at least two separate retinal stimuli to the single digitally addressed optical modulation element; and

[0101] - A second optical path deflector configured to separate at least two separate phase maps of at least two separate regions to be projected onto the retina of a human eye.

[0102] Example 11. The device according to the previous embodiment, wherein each of the first optical path diverter and the second optical path diverter includes at least two mirrors and at least one prism.

[0103] Example 12. The device according to any of the foregoing embodiments further includes:

[0104] - At least two separate displays, each configured to provide at least one separate retinal stimulation.

[0105] Example 13. The device according to the previous embodiment further includes:

[0106] - A separate digitally addressed optical modulation element configured to generate one of the at least two separate phase maps.

[0107] Example 14. The device according to the preceding two embodiments, wherein a separate display is configured to provide the at least one separate retinal stimulus to a corresponding separate digitally addressed optical modulation element.

[0108] Example 15. The device according to the previous embodiment further includes:

[0109] - At least one first optical relay system, which is configured to provide the at least one individual retinal stimulus to a corresponding individual digitally addressed optical modulation element.

[0110] Example 16. The device according to the previous embodiment further includes:

[0111] - At least one Badal level, which is configured to correct out-of-focus errors.

[0112] Example 17. The device according to the previous embodiment, wherein the at least one Badal stage is incorporated into the at least one optical relay system.

[0113] Example 18. The device according to any of the foregoing embodiments further includes:

[0114] - At least one refractive correction element, particularly the at least one non-pixelated correction element, the at least one refractive correction element being configured to generate one of the at least two separate phase maps.

[0115] Example 19. The device according to any of the foregoing embodiments further includes:

[0116] - At least one ocular aberration meter, the at least one ocular aberration meter being configured to determine at least one value of ocular aberration at at least two separate areas on the retina of a human eye by using reflected light received from at least two separate areas on the retina of a human eye.

[0117] Example 20. The device according to the previous embodiment, wherein the at least one eye aberration meter is configured to determine at least one value of refractive effect associated with at least two separate areas on the retina of a human eye.

[0118] Example 21. The device according to any of the first two examples, wherein the device includes a separate eye aberration meter for each different degree of retinal eccentricity.

[0119] Example 22. The device according to any one of the first three examples, wherein the device includes a single eye aberration meter for at least two different retinal eccentricities.

[0120] Example 23. The device according to any one of the first four examples, wherein the at least one eye aberration meter is or includes at least one wavefront sensor, particularly at least one Hartmann-Shack wavefront sensor (HSWS).

[0121] Example 24. The device according to any one of the preceding five examples further includes:

[0122] - At least one light source, which is configured to generate at least one light beam used in determining at least one value of the eye aberration.

[0123] Example 25. The device according to the previous embodiment, wherein the at least one aberration meter is configured to determine at least one value of the aberration at at least two separate regions on the retina of a human eye by using a portion of reflected light generated by the at least one light source and received from at least two separate regions on the retina of a human eye.

[0124] Example 26. The device according to any one of the first two examples, wherein at least one light source is or includes an IR light source, particularly an IR light-emitting diode.

[0125] Example 27. The device according to any of the foregoing embodiments further includes:

[0126] - At least two polarizers configured to suppress specular reflections on the cornea of ​​the human eye.

[0127] Example 28. The device according to the previous embodiment, wherein the at least two polarizers are placed in front of at least one of the eye aberration meter, particularly the Hartmann-Shack wavefront sensor (HSWS), and the light source, preferably the IR light source, particularly the IR light-emitting diode.

[0128] Example 29. The device according to any of the foregoing embodiments, wherein the measuring device for capturing choroidal topography on at least two separate regions of the retina of a human eye is or includes an optical coherence tomography (OCT) system.

[0129] Example 30. The apparatus according to the previous embodiment, wherein the optical coherence tomography (OCT) system is configured to perform at least one of Fourier domain OCT, swept-source OCT, or time-domain OCT.

[0130] Example 31. The device according to any of the foregoing embodiments further includes:

[0131] - At least one camera, which is configured to determine the alignment of a person's eyes.

[0132] Example 32. The device according to any of the foregoing embodiments further includes:

[0133] - A processing device configured to control at least one element of the device and to determine the effect of at least one ophthalmic lens design on the choroidal topography.

[0134] Example 33. Use of the device according to any of the foregoing embodiments for determining the effect of at least one ophthalmic lens design on choroidal topography.

[0135] Example 34. A method for projecting retinal stimulation onto a region of the retina of a human eye and for determining choroidal topography on a region of the retina of a human eye, the method comprising the following steps:

[0136] a) Projecting a phase map onto a region of the retina of a human eye using at least one optical transmission element, wherein the phase map includes a modified retinal stimulus;

[0137] b) Separating the reflected light received from the region on the retina of the human eye from the phase map projected onto the region on the retina of the human eye using an optical filter; and

[0138] c) By using a measuring device, a choroidal topography map of the area on the retina of the human eye is captured using reflected light received from the area on the retina of the human eye.

[0139] The process involves generating at least two separate phase maps, wherein each separate phase map is projected onto one of at least two separate regions on the retina of a human eye using the at least one optical transmission element, wherein at least one of the two separate regions is a peripheral region on the retina of a human eye, extending beyond the fovea on the retina of a human eye.

[0140] Example 35. The method according to the previous embodiment, wherein each individual phase map is simultaneously projected onto more than one region in at least two individual regions on the retina of a human eye.

[0141] Example 36. The method according to any of the foregoing method embodiments further includes the following steps:

[0142] d) By using a digitally addressed optical modulation element, at least one phase map among these individual phase maps is generated by modifying at least one imaging characteristic of the retinal stimulus;

[0143] Example 37. The method described in any of the foregoing method embodiments further includes the following steps:

[0144] e) To provide at least two separate retinal stimuli by using at least two displays to generate the at least two separate phase maps.

[0145] Example 38. The method described in any of the foregoing method embodiments further includes the following steps:

[0146] f) By using at least one eye aberration meter, at least one value of the eye aberration at at least two separate areas of the retina of a human eye is determined using reflected light received from at least two separate areas of the retina of a human eye.

[0147] Example 39. The method described in the preceding method embodiment further includes the following steps:

[0148] g) Generate at least one light beam used in determining at least one value of the eye aberration by using at least one light source;

[0149] Example 40. The method according to any of the foregoing method embodiments further includes the following steps:

[0150] h) Determine the alignment of a person's eyes by using at least one camera. Attached Figure Description

[0151] Preferably, other optional features and embodiments of the invention are disclosed in more detail in the following description of the preferred embodiments, in conjunction with the dependent claims. These optional features, as will be recognized by those skilled in the art, can be implemented in isolation and in any feasible combination. It is emphasized here that the scope of the invention is not limited to the preferred embodiments disclosed herein. In the accompanying drawings:

[0152] Figures 1 to 4 Each illustrates an embodiment of the device according to the invention;

[0153] Figure 5 Embodiments of the method according to the present invention are shown; and

[0154] Figure 6 and Figure 7 Each of these presents another embodiment of the device according to the invention. Detailed Implementation

[0155] Figure 1An embodiment of the device 110 according to the invention is illustrated, which is configured to project retinal stimuli 112, 112' onto regions 114, 114' of the retina 116 of a human eye 117 and / or to determine choroidal topography on at least regions 114, 114' of the retina 116 of the human eye 117. As described in more detail elsewhere herein, the device 110 can be particularly used to determine the effect of ophthalmic lens design on choroidal topography, especially under short-duration retinal stimulation, preferably within a range of minutes, in such a way that short-term results can be used to predict long-term effects, thereby allowing optimization of ophthalmic lens design prior to clinical studies.

[0156] like Figure 1 As schematically depicted, device 110 has a first module 118 comprising digitally addressed optical modulators 120, 120', each configured to generate a separate phase map. For this purpose, two independent and distinct retinal stimuli 112, 112' are preferably emitted simultaneously by two separate displays 122, 122' and relayed to the inlets of the digitally addressed optical modulators 120, 120' using correspondingly adapted first optical relay systems 124, 124'. As described in more detail above, the digitally addressed optical modulators 120, 120' are designed to modulate the incident retinal stimuli 112, 112' provided by the respective displays 122, 122', and may preferably be selected from spatial light modulators (SLMs) or digital micromirror devices (DMDs); however, the use of different types of digitally addressed optical modulators may also be feasible.

[0157] like Figure 1 As further schematically depicted, the first module 118 of the device further includes two first optical transmission elements 126, 126', each of which is configured to project a separate phase map onto regions 114, 114' of the retina 116 of a human eye 117. For this purpose, each separate phase map provided at the exit of each digitally addressed optical modulation element 120, 120' is transmitted to the first optical transmission elements 126, 126' by using a correspondingly adapted second optical relay system 130, 130', each of which is here implemented as a beam splitter 128, 128'.

[0158] Each of the first optical transmission elements 126, 126' is configured to project a corresponding individual phase map onto a corresponding region 114, 114' of the retina 116 of a human eye 117. Further, as a second optical transmission element configured to simultaneously project each of at least two individual phase maps with different retinal eccentricities onto each of at least two individual regions 114, 114' (i.e., the foveal region and the peripheral region) of the retina, cold reflectors 162, 162' are used. Figure 1 As further illustrated, central retinal stimulation 132 (schematically depicted herein as a puppy) is projected onto a first separate region 134, wherein the first separate region 134 includes a fovea 136 located on the retina 116 of the human eye 117. Additionally, peripheral retinal stimulation 132' (schematically depicted herein as a checkered pattern) is projected onto a second separate region 134', wherein the second separate region 134' is located outside the fovea 136 on the retina 116 of the human eye 117. Preferably, the second separate region 134' is further located outside the region including the optic nerve 138 of the human eye 118.

[0159] like Figure 1 Further schematically depicted, device 110 has a second module 140, which includes a measuring device 142 configured to capture choroidal topography, and in particular choroidal layer thickness, on regions 114 and 114' of the retina 116 of a human eye 117 by using reflected light received from regions 114 and 114' on the retina 116. As depicted herein, measuring device 142 includes an optical coherence tomography (OCT) system 144, supplemented herein by a scanning device 146 configured to change the direction of the optical axis and interrogate different regions of the retina 116 of the human eye 117; however, it may also be feasible to use different types of measuring devices. For the purpose of guiding incident light, including individual phase maps, to corresponding regions 114, 114' on the retina 116 of the human eye 117 and guiding reflected light received from regions 114, 114' on the retina 116 of the human eye 117, the second module 140 further includes a light path diverter 148, which includes two parabolic mirrors 150, 150', such as Figure 1 As further illustrated. However, it is also feasible to replace at least one of the parabolic mirrors 150 and 150' with an achromatic lens.

[0160] like Figure 1As further schematically depicted, the second module 140 further includes an optical filter 152 configured to separate reflected light received from regions 114, 114' on the retina 116 of the human eye 117 from each individual phase map of the corresponding regions 114, 114' to be projected onto the retina 116 of the human eye 117. Figure 1 As depicted, the dichroic mirror 154 is used for this purpose; however, it is also feasible to use different types of optical filters. In this way, the device 110 is configured to both project retinal stimuli 112, 112' onto separate regions 114, 114' of the retina 116 of the human eye 117 and to determine choroidal topography on separate regions 114, 114' of the retina 116 of the human eye 117.

[0161] In addition, such as Figure 1 The illustrated device 110 is further equipped with aberration meters 156, 156', which are configured to determine the value of the aberration at individual regions 114, 114' on the retina 116 of a human eye 117 by using reflected light received from regions 114, 114' on the retina 116 of the human eye 117. For this purpose, each aberration meter 156, 156' includes a wavefront sensor, specifically a Hartmann-Shack wavefront sensor (HSWS) 158, 158'; however, different types of aberration meters can be envisioned. A light source 160, 160' is provided to generate the light beam used in determining the value of the aberration measurement. Figure 1 Each of the depicted light sources 160, 160' includes an IR light source, specifically an IR light-emitting diode; however, it is also possible to use different types of light sources. Cold reflectors 162, 162' are used to guide the IR light emitted from the light sources 160, 160' to regions 114, 114' on the retina 116 of the human eye 117. Optical filters 152, optical transmission elements 126, 126', and cold reflectors 162, 162' are used to guide the reflected IR light from regions 114, 114' on the retina 116 of the human eye 117. However, it is also possible to use different arrangements.

[0162] In addition, such as Figure 1The illustrated device 110 is further equipped with cameras 164, 164', which are configured to determine the alignment of each of the person's eyes 117. In this way, high-quality measurements can be ensured, in particular, by monitoring the pupil of each of the person's eyes 117. As further depicted herein, IR light-emitting diodes 166, 166', invisible to the human eye 117, are employed during the projection of the phase map onto regions 114, 114' on the retina 116 of the human eye 117 and the capture of choroidal topography on regions 114, 114' on the retina 116 of the human eye 117.

[0163] like Figure 1 Further schematically depicted, device 110 includes a processing unit 168 configured to both control modules 118, 140 of the device and determine the influence of at least one ophthalmic lens design on choroidal topography. For the latter purpose, input data including values ​​of the choroidal topography can be used to determine the influence of at least one ophthalmic lens design on the choroidal topography. Additionally, processing unit 168 can be used for other purposes.

[0164] Figure 2 Another embodiment of the device 110 according to the invention is shown, which is configured to project retinal stimuli 112, 112' onto regions 114, 114' of the retina 116 of a human eye 117 and / or to determine choroidal topography on at least regions 114, 114' of the retina 116 of the human eye 117. (The last sentence appears to be incomplete and possibly refers to a different embodiment.) Figure 1 Compared to the described embodiments, Figure 2 The embodiment uses only a single digitally addressed optical modulation element 120. A third optical transmission element 170, including a first single prism 172 and two mirrors 174, 174', is configured to guide light emitted by the respective displays 122, 122' to be modulated in corresponding halves of the single digitally addressed optical modulation element 120. Further, a second optical transmission element 176, including a single second prism 178 and two mirrors 174, 174', is configured to simultaneously project each of at least two separate phase maps with different retinal eccentricities onto each of at least two separate regions 134, 134' of the retina 116 of the human eye 117 at a specific retinal eccentricity. Furthermore, the reflected light from the retina 116 is used here to determine the choroidal topography by using a measuring device 142 including an optical coherence tomography system (OCT) 144, and to determine the ocular aberrations at individual regions 114, 114' on the retina 116 by using a single ocular aberrometer 156 including a single Hartmann-Shack wavefront sensor (HSWS) 158 as a wavefront sensor.

[0165] Figure 3 Another embodiment of the device 110 according to the invention is shown, which is configured to project retinal stimuli 112, 112' onto regions 114, 114' of the retina 116 of a human eye 117 and / or to determine choroidal topography on at least regions 114, 114' of the retina 116 of the human eye 117. (The last sentence appears to be incomplete and possibly refers to a different embodiment.) Figure 1 Compared to the described embodiments, Figure 3 The embodiment uses a rotating beam splitter (RBS) 180 as a second optical transmission element, which is configured to project each of these individual phase maps with different retinal eccentricities onto each individual region 114, 114' of the retina 116 of the human eye 117. In this way, this embodiment provides a configuration with variable eccentricity along the horizontal meridian of the peripheral retinal stimulus 132'. Herein, the beam used in determining the value of the eye aberration measurement is rotated together with the beam carrying the peripheral retinal stimulus 132'. Further, the beam is here directed to the human eye 117 using two separate optical path diverters 148, 148', each optical path diverter having a parabolic mirror 150, 150' and a dichroic mirror 154 placed between the optical path diverters 148, 148'.

[0166] As for Figure 2 or Figure 3 Further details of the embodiments can be found in the description of the embodiments. Figure 1 Description of the embodiments.

[0167] Figure 4 Another embodiment of the device 110 according to the invention is shown, which is configured to project retinal stimuli 112, 112' onto regions 114, 114' of the retina 116 of a human eye 117 and / or to determine choroidal topography on at least regions 114, 114' of the retina 116 of the human eye 117. Similarly, Figure 4 The embodiment uses a rotating beam splitter (RBS) 180 as a second optical transmission element, which is configured to project each of these individual phase maps with different retinal eccentricities onto each individual region 114, 114' of the retina 116 of the human eye 117. (The last sentence appears to be incomplete and possibly refers to a different implementation.) Figure 3 Compared to the described embodiments, Figure 4The embodiment is configured to project a wide field of view (FOV) stimulus 182 as a central retinal stimulus 132, which is used here to provide a more natural viewing experience to a person. For this purpose, a refractive corrective element, particularly at least one non-pixelated corrective element 184 (i.e., an element with the ability to change the phase map of the beam, wherein the surface of this element is not divided into pixels, particularly selected from deformable mirrors, a single optical lens, or a group of optical lenses, configured to generate corresponding individual phase maps), can be used instead of a spatial light modulator (SLM) or a digital micromirror device (DMD), thereby avoiding the potential limitation of the wide field of view. In addition, the stimulus is darkened in region 114 of the peripheral retinal stimulus 132', the eccentricity of which can be changed by using a rotating beam splitter 180. Further, the two parabolic mirrors 150, 150' and the rotating beam splitter 180 included in another optical path deflector 148" are used to combine the beams of each retinal stimulus 112, 112'.

[0168] As for Figure 4 Further details of the embodiments can be found in the description of the embodiments. Figure 3 Description of the embodiments.

[0169] Figure 5 An embodiment of the method 210 according to the invention is shown, which is used to project retinal stimuli 112, 112' onto regions 114, 114' on the retina 116 of a human eye 117 and / or to determine choroidal topography 218 on at least regions 114, 114' on the retina 116 of a human eye 117.

[0170] In projection step 212 according to step b), a phase map is projected onto regions 114, 114' of the retina 116 of a human eye 117 using optical transmission elements 126, 126' as described in more detail above. Hereinafter, each individual phase map is projected onto one of the individual regions 114, 114' of the retina 116 of the eye 117, wherein one region 114' is a peripheral region of the retina 116 of the human eye 117 that extends beyond the fovea 136. Preferably, individual phase maps are simultaneously projected onto at least one individual region 114, 114' of the retina 116 of the human eye 117.

[0171] In separation step 214 according to step b), the reflected light received from regions 114, 114' on the retina 116 of the human eye 117 is separated from the phase map of regions 114, 114' projected onto the retina 116 of the human eye 117.

[0172] In the capture step 216 according to step c), at least the choroidal topography 218 on the regions 114, 114' of the retina 116 of the human eye 117 is captured by using the measuring device 142 as described in more detail above, by using reflected light received from regions 114, 114' on the retina 116 of the human eye 117.

[0173] In the optional generation step 220 according to step d), prior to the projection step 212, at least one of these individual phase maps is generated by modifying at least one imaging characteristic of the retinal stimuli 112, 112', preferably by using digitally addressed optical modulation elements 120, 120' as described in more detail above.

[0174] In the optional provisioning step 222 according to step e), two separate retinal stimuli 112, 112' are provided by generating two separate phase maps using two displays 122, 122', prior to projection step 212 and (if applicable) generation step 220.

[0175] In the optional determination step 224 according to step f), in parallel with the capture step 216, at least one ocular aberration value at a separate region 114, 114' on the retina 116 of the human eye 117 is determined by using one or two aberrometers 156, 156', preferably comprising one or two Hartmann-Shack wavefront sensors (HSWS) 158. For this purpose, at least one light beam can be generated in another optional IR light generation step 226 according to step g), using light sources 160, 160' as described in more detail above, for use in determining at least one value of ocular aberration according to determination step 224.

[0176] In the optional alignment step 228 according to step h), the alignment of the human eye 117 is determined, preferably in parallel with the projection step 212, the separation step 214 and the capture step 216, preferably by using cameras 164, 164' as described in more detail above.

[0177] Figure 6Another embodiment of the device 110 according to the invention is shown, which is configured to project retinal stimuli 112, 112' onto regions 114, 114' of the retina 116 of a human eye 117 and / or to determine choroidal topography on regions 114, 114' of at least the retina 116 of a human eye 117, wherein a second optical path diverter is shared between a first module 118 and a second module 140. This embodiment includes four lenses 177, two prisms 178, 178', and four mirrors 179. Hereinafter, the second optical path diverter also acts as a second optical transmission element 176, which is configured to project each of these individual phase maps with different retinal eccentricities onto each individual region 114, 114' of the retina 116 of a human eye 117. In the first module 118, beams corresponding to each retinal stimulus are dispersed in different directions by prism 178. These beams are modulated by digitally addressed optical modulators 120, preferably selected from spatial light modulators (SLMs) or digital micromirror devices (DMDs). Each beam is guided by corresponding mirrors 179, 179' to an optical lens 177, 177'. After passing through lenses 179, 179', two movable mirrors 179"', 179"' (as indicated by corresponding arrows) guide the beams to prism 178". After passing through prism 178', the beams propagate in parallel, separated from each other by the distance given by the two movable mirrors 179"', 179"'. The separated beams then pass through optical lens 177" located in the second module 140, thereby illuminating the pupil of the human eye 117 with different degrees of eccentricity. The eccentricity of each beam is provided by the following:

[0178] arctan(d / f),

[0179] In the formula, arctan() represents the tangent function, f represents the focal length of the optical lens 177” after the dichroic mirror 154 in the second module 140, and d represents the distance between the center of the beam and the center of the optical lens 177”. In the second module 140, another optical lens 177”’ located after the scanning device 146 propagates the beam from the measuring device 142, which includes the optical coherence tomography (OCT) system 144, parallel to the optical axis of the other optical lens 177”’. The dichroic mirror 154 guides the beam to the optical lens 177”’, thereby forming a second optical path diverter, which is shared between the first module 118 and the second module 140 of the device 110.

[0180] Figure 7Another embodiment of the device 110 according to the invention is shown, configured to project retinal stimuli 112, 112' onto regions 114, 114' of the retina 116 of a human eye 117 and / or to determine choroidal topography on regions 114, 114' of at least the retina 116 of a human eye 117. This embodiment can be configured to supplement all described embodiments to project polychromatic retinal stimuli 112, 112' having independent image characteristics at different wavelengths. For this purpose, polychromatic retinal stimuli 112, 112' are generated and combined via temporal multiplexing. Figure 7 As schematically depicted, the polychromatic retinal stimuli 112, 112' can preferably be generated using one or more laser devices 190, 190', 190" (preferably laser diodes) having red (R), green (G), and blue (B) wavelengths. However, it is also conceivable to use different types of devices for generating the polychromatic retinal stimuli 112, 112' and / or other wavelengths. For each retinal eccentricity, the stimulation can be shaped using one display for each wavelength or one display for all wavelengths. Figure 7 In an exemplary embodiment, each display 122, 122' is configured to emit retinal stimuli 112, 112' for all wavelengths of red (R), green (G), and blue (B). The displays 122, 122' may preferably be selected from liquid crystal-based or digital micromirror-based displays; however, it is also feasible to use different displays.

[0181] A trichromatic prism 192 guides a monochromatic beam along a common path 194. A variable filter 196 can be used to split a portion of the monochromatic beam to a synchronization device 198, which is configured to drive a monochromatic illumination sequence centered on each wavelength within time t. Further, the synchronization device 198 is configured to trigger displays 122, 122' and a digitally addressed optical modulator 120 (preferably selected from spatial light modulators (SLMs) or digital micromirror devices (DMDs)) to project intensity maps and corresponding phase maps of multichromatic retinal stimuli 112, 112', the phase maps being configured to modify the image characteristics of the multichromatic retinal stimulation for each wavelength. The wavelength dependence of the performance of the digitally addressed optical modulator 120 can be adjusted by projecting an optimized phase map onto each wavelength after calibrating the phase modulation of the digitally addressed optical modulator 120 at each wavelength. Especially in liquid crystal-based SLMs, phase modulation refers to the phase delay caused by the voltage applied to the liquid crystal cell. This voltage can be addressed via grayscale, which can be programmed in the video card of the processing device 168.

[0182] List of reference numerals

[0183] 110 equipment

[0184] 112' retinal stimulation

[0185] Areas 114 and 114'

[0186] 116 Retina

[0187] 117 Eyes

[0188] 118 Module 1

[0189] 120 Digitally Addressable Optical Modulation Element

[0190] 122" monitor

[0191] 124, 124' First Optical Relay System

[0192] 126, 126' Optical transmission elements

[0193] 128' and 128' beam splitters

[0194] 130, 130' Second Optical Relay System

[0195] 132-center retinal stimulation

[0196] 132' Peripheral retinal stimulation

[0197] 134 The first separate area

[0198] 134' Second separate area

[0199] 136 Central concave

[0200] 138 Optic Nerve

[0201] 140 Module Two

[0202] 142 Measuring device

[0203] 144 Optical Coherence Tomography (OCT) System

[0204] 146 Scanning device

[0205] 148", 148', 148” optical path steering

[0206] 150° and 150° parabolic mirrors

[0207] 152 Optical Filter

[0208] 154 Dichroic Mirror

[0209] 156' and 156' eye aberration meters

[0210] 158' Hartmann-Shack wavefront sensor (HSWS)

[0211] 160' light source

[0212] 162' and 162' cold reflective mirrors

[0213] 164" camera

[0214] 166' IR LED

[0215] 168 processing unit

[0216] 170 Third optical transmission element

[0217] 172 First Single Prism

[0218] 174' and 174' reflectors

[0219] 176 Second optical transmission element

[0220] 177' Optical lenses (in the first module)

[0221] 177”, 177”' optical lenses (in the second module)

[0222] 178' Second Prism

[0223] 179' and 179' reflectors

[0224] 179” and 179”' movable reflectors

[0225] 180° Rotating Beam Splitter (RBS)

[0226] 182 Wide Field of View (FOV) Stimulation

[0227] 184 non-pixelated correction elements

[0228] 186 Infrared Diode Laser

[0229] 188, 188' infrared beam

[0230] 190, 190', 190” laser device

[0231] 192 Tricolor Prism

[0232] 194 Path

[0233] 196 Variable filter

[0234] 198 Synchronization device

[0235] 210 Method

[0236] 212 Projection Steps

[0237] 214 Separation Steps

[0238] 216 Capture Steps

[0239] 218 Choroidal Topographic Map

[0240] 220 Generation Steps

[0241] 222 provides steps

[0242] 224 Determine the steps

[0243] 226 IR light generation steps

[0244] 228 Alignment Steps

Claims

1. A device (110) configured to determine a choroidal topography (218) on a region (114, 114') of the retina (116) of a human eye (117), the device comprising: - At least two optical transmission elements, including a first optical transmission element and a second optical transmission element, each of the at least two optical transmission elements being configured to project at least one of a retinal stimulus (112, 112') or a phase map onto a region of the retina of a human eye, wherein the phase map includes a modified retinal stimulus; - A measuring device (142) for capturing a choroidal topography (218) on the region (114, 114') of the retina (116) of the person's eye (117) by using reflected light received from the region (114, 114') on the retina (116) of the person's eye (117). - An optical filter (152) configured to separate the reflected light received from a region (114, 114') on the retina (116) of the person's eye (117) from the phase map of the region (114, 114') projected onto the retina of the person's eye (117). Its features are, The device (110) further includes: - At least two separate displays (122, 122'), each of which is configured to provide the retinal stimulation (112, 112'), thereby providing two independent retinal stimuli (112, 112'). The second optical transmission element is further configured to simultaneously project each of the at least two separate phase maps onto each of at least two separate regions (134, 134') on the retina (116) of the person's eye (117) with different retinal eccentricities, wherein these separate regions (134, 134') include a peripheral region and a foveal region on the retina (116) of the person's eye (117).

2. The device (110) according to claim 1, characterized in that, The second optical transmission element is or includes at least one of a mirror, a beam splitter, a rotating beam splitter (180), or a diffractive element.

3. The device (110) according to claim 1 or 2, characterized in that, The second optical transmission element is a rotating beam splitter (180).

4. The device (110) according to claim 3, characterized in that, Further includes: - At least one telescope (148) configured to direct each of the at least two separate phase maps to a corresponding separate area (134, 134') on the retina (116) of the person's eye (117).

5. The device (110) according to claim 1 or 2, characterized in that, Further includes: - A scanning device (146) configured to change the direction of the optical axis relative to the retina (116) of the person's eye (117).

6. The device (110) according to claim 1 or 2, characterized in that, Further includes: - At least one digitally addressable optical modulation element (120, 120') configured to generate the at least two individual phase maps by modifying at least one imaging characteristic of the at least two retinal stimuli.

7. The device (110) according to claim 6, characterized in that, include: - A single digitally addressable optical modulation element (120) configured to generate at least two phase maps of these individual phase maps.

8. The device (110) according to claim 7, characterized in that, Further includes: - A third optical transmission element (170) configured to provide at least two separate retinal stimuli (114, 114') to the single digitally addressable optical modulation element (120).

9. The device (110) according to claim 6, characterized in that, It includes at least two digitally addressable optical modulation elements (120, 120'), wherein each of these digitally addressable optical modulation elements (120, 120') is assigned to each of these retinal stimuli (112, 112') and is configured to generate a separate phase map, respectively.

10. The device (110) according to claim 1 or 2, characterized in that, The separate display (122, 122') for providing the retinal stimulation (112, 112') to the foveal region of the retina (116) of the eye (117) is configured to provide wide field-of-view stimulation.

11. The device (110) according to claim 10, characterized in that, It further includes at least one non-pixelated correction element (184) configured to generate a phase map by modifying the image characteristics of the wide field-of-view stimulus.

12. Use of the device (110) according to claim 1 or 2 for determining the effect of at least one ophthalmic lens design on choroidal topography (218).

13. A method (210) configured to determine a choroidal topography (218) on a region (114, 114') of the retina (116) of a human eye (117), the method comprising the steps of: a) Projecting a phase map onto a region (114, 114') of the retina of a human eye using at least one optical transmission element, wherein the phase map includes a modified retinal stimulus (112, 112'). b) By using an optical filter (152), the reflected light received from the region (114, 114') on the retina (116) of the person's eye (117) is separated from the phase map projected onto the region (114, 114') on the retina (116) of the person's eye (117); and c) By using a measuring device (142), a choroidal topography (218) is captured on the area (114, 114') of the retina (116) of the person's eye (117) by using the reflected light received from the area on the retina (116) of the person's eye (117). Its features are, By using at least two separate displays (112, 112') to provide at least two independent retinal stimuli (112, 112'), and by simultaneously projecting each of the at least two separate phase images with different retinal eccentricities onto each of at least two separate regions (134, 134') on the retina (116) of the person's eye (117), wherein the at least two separate regions (134, 134') include the peripheral region and the foveal region on the retina (116) of the person's eye (117).

14. The method (210) of claim 13, further comprising at least one of the following steps: d) By using digitally addressable optical modulation elements (120, 120'), at least one phase map among these individual phase maps is generated by modifying at least one imaging characteristic of the retinal stimulus (112, 112'); e) By using at least one ocular aberration meter (156, 156'), the ocular aberration at at least two separate areas (134, 134') on the retina (116) of the person's eye (117) is determined by using reflected light received from at least two separate areas (134, 134') on the retina (116) of the person's eye (117); f) Generate at least one light beam used in determining at least one value of the eye aberration by using at least one light source (160, 160'); g) Determine the alignment of the person’s eyes (117) by using at least one camera (164, 164').

Images