Device for projecting images on retina

Abstract

To provide a favorable device for projecting images on a retina.SOLUTION: A device for stimulating a retina comprises one or more light sources coupled to one or more optical elements. The one or more optical elements are configured to illuminate the retina with one or more images at a location away from a fovea of a wearer. In some embodiments, each of the one or more images comprises a depth of focus and a spatial resolution. The one or more images can be formed at a distance anterior to the retina, at a distance posterior to the retina, or on the retina. In some embodiments, the depth of focus is less than the distance, and the spatial resolution is greater than a spatial resolution of the retina at the location.SELECTED DRAWING: Figure 1

Description

[Background technology]

[0001] (Related Applications) This application is a continuation of U.S. Provisional Patent Application No. 62 / 925,948, filed October 25, 2019 and entitled "DEVICE FOR PROJECTING IMAGES ON THE RETINA," U.S. Provisional Patent Application No. 62 / 907,496, filed September 27, 2019 and entitled "DEVICE FOR PROJECTING IMAGES ON THE RETINA," U.S. Provisional Patent Application No. 62 / 885,035, filed August 9, 2019 and entitled "SPECTACLE LENSES WITH NEAR EYE DISPLAYS FOR PREVENTION OF MYOPIA PROGRESSION," and U.S. Provisional Patent Application No. 62 / 885,035, filed July 31, 2019 and entitled "SPECTACLE LENSES WITH NEAR EYE DISPLAYS FOR PREVENTION OF MYOPIA PROGRESSION," the entire disclosures of which are incorporated herein by reference under 35 U.S.C. §119(e). This application claims the benefit of U.S. Provisional Patent Application No. 62 / 881,123, entitled "PREVENTION OF MYOPIA PROGRESSION."

[0002] (background) Myopia, or nearsightedness, is a refractive error in which distant objects are focused in front of the retina. It can be related to the axial length of the eye. Generally, a 1.0 mm increase in the axial length of the eye corresponds to an increase in myopia of 2.5 diopters ("D").

[0003] Spectacle lenses, contact lenses, and refractive surgery can be used to treat refractive errors of the eye, such as myopia. Although these approaches can be effective in treating myopia, the eye may continue to grow axially, such that the amount of myopia continues to increase. The relatively high prevalence of myopia has prompted research to understand the underlying mechanisms of axial growth and the development of potential treatments that target axial growth.

[0004] Although myopia is known to have a genetic cause, the dramatic increase in the incidence of myopia cannot be explained by genetic factors alone; rather, they must be interpreted as just that, a remarkable ability of the visual system to adapt to altered environmental conditions; specifically, a shift in visual habits from long distances to short distances and from open to enclosed spaces.

[0005] It is known that the retina of many species, including humans, responds to defocused images and grows to minimize the blur caused by defocus. Although the mechanism of growth signal generation is still under investigation, one of the observable phenomena of retinal tissue response to growth signals is the change in choroidal thickness. Myopically defocused images can cause the choroid to grow thicker, thus effectively shortening the axial length of the eye, while hyperopically defocused images can cause the choroid to grow thinner, leading to an increase in axial length. The writings related to this disclosure suggest that the change in axial length caused by the retinal response to hyperopic blur or defocus can contribute to the development of myopia.

[0006] Image defocus may play a role in the change of choroidal thickness and axial length of eye, but previous methods and devices are sub-ideally suitable for dealing with the change of retinal thickness and axial length of eye.For example, pharmaceutical treatments have been suggested to treat myopia associated with axial length growth, but these treatments may have sub-ideal results at least in some cases.Atropine and other muscarinic agonists may slow down myopia deterioration, but possible concerns about rebound effect after treatment and short- and long-term side effects associated with long-term treatment may prevent widespread use of these drugs.

[0007] Although animal studies have demonstrated that visual development and axial growth can be regulated by visual feedback linked to the effective refractive status of the eye, the methods and devices used in these animal studies are sub-ideally suitable for the treatment of myopia in humans.

[0008] The writings related to this disclosure suggest that the retinal shell becomes more aspheric as the eye becomes more myopic. An example of an image shell on the retina and conventional correction with a myopic eye is described in Cooper, J, "A Review of Current Concepts of the Etiology and Treatment of Myopia" in Eye & Contact Lens, 2018;44:pp231. With a conventional spherical lens, the peripheral aspheric retina of a myopic eye receives light that is focused behind the retina while the light is focused at the center of the retina, which may trigger a growth signal as peripheral light is focused behind the retina, similar to an eye with insufficient axial length. Conventional spherical or toric lenses (e.g., contact lenses or spectacle lenses) generally cannot generate an image shell that matches the optimal shape required for refractive correction, which would stop the growth signal to the retina and become even more myopic. One approach has been to provide an aspheric lens that focuses light onto the peripheral region of an aspheric retina.

[0009] Previous refractive correction devices for preventing myopia progression may produce sub-ideal results, at least in some cases. Refractive correction to provide the proper focus to the peripheral retina may require a highly aspheric image shell, which may be created by a highly aspheric optical system. Unfortunately, such aspheric optical systems may produce a central image with substantial aberrations, at least in some cases, impairing distance vision and reducing the quality of the wearer's vision. One approach has been to limit the amount of asphericity to about 2D or less to provide distance vision without significant aberrations for central vision, but this limit on the amount of asphericity may also limit the amount of correction to the peripheral portion of the retina, which may lead to sub-ideal treatment in some cases.

[0010] A second approach, adopted by some prior art devices, is to provide bifocal or multifocal optics with a central optical zone dedicated solely to the correction of refractive error, while the peripheral zone generally has an additional + refractive power to myopically form a defocused image on the peripheral retina. Ray tracing analysis shows that these bifocal optics can create one or more foci at the fovea, compromising image quality at the fovea.

[0011] Studies in animal models as well as clinical studies suggest that the retina may be able to distinguish between "+ blur" and "- blur" or image blur caused by myopic and hyperopic defocus, potentially by using longitudinal chromatic aberration as a guide, since the sign of the longitudinal chromatic aberration will be opposite depending on whether the image blur is hyperopic or myopic. However, previous clinical approaches may not adequately address chromatic aberration to reduce myopic deterioration, at least in some cases.

[0012] Thus, new approaches are needed to treat ocular refractive errors and facilitate changes in the axial length and choroidal thickness of the eye that ameliorate at least some of the limitations of previous approaches. Summary of the Invention [Means for solving the problem]

[0013] (summary) In some embodiments, the device for stimulating the retina is configured to project one or more images onto the retina, which corresponds to the outside of the fovea. The stimulation can be configured to encourage changes in the axial length of the eye and / or the choroidal thickness. The projected images may comprise static images or dynamic images, for example, with a refresh rate in the range of 1 Hz to 500 Hz. The light may comprise monochromatic or polychromatic light in the range of 400 nm to 800 nm. The one or more images can be configured in many ways with an image structure corresponding to the information or content of the image associated with a spatial frequency. In some embodiments, the one or more images comprise a spatial frequency in the range of 1 cycle / degree to 180 cycles / degree, or 1 cycle / degree to 30 cycles / degree, or 1 cycle / degree to 10 cycles / degree, and a contrast in the range of 99.9% to 2.5%, for example. The projected images can be projected onto the retina with an eccentricity relative to the fovea, which can be in the range of 5 degrees to 40 degrees. The projected image may cover the entire retina, for example with an annular pattern, within a defined range of eccentricity, or the projected image may cover a portion of the retina within that range of eccentricity. The stimulus may be continuous or periodic or aperiodic. When periodic, the stimulus may last for a duration in the range of 1 second to 24 hours. The stimulus may be applied in many ways, for example, when the subject is awake or asleep and combinations thereof. The retinal stimulus may be applied using an optical projection system. The optical projection system may be configured in many ways and is suitable for combination with one or more of many devices. The projection optics as described herein may be integrated into one or more of a projector, an ophthalmic instrument, a TV screen, a computer screen, a handheld device such as a smartphone, a wearable device such as a spectacle lens, an ocular display, a head mounted display, goggles, a contact lens, a corneal onlay, a corneal inlay, a keratoprosthesis, or an intraocular lens. For example, the projection optics may be combined with a combination of these devices.

[0014] In some embodiments, a device for stimulating the retina comprises a light source and an optical system for forming an image in front of, behind, or on the retina with one or more of the appropriate resolution, focal depth, or diffraction. The image formed on a region of the retina may have a resolution finer than the resolution of the retina in that region, such as the highest resolution of the retina in that region. The light beam can be directed to a region of the retina at an angle relative to the optical axis of the eye to illuminate an outer portion of the retina away from the fovea with a finer resolution than the corresponding location of the retina. The focal depth can be configured to illuminate the retina with an appropriate amount of blurring of the image on the retina, and the diffraction of the spot can be appropriately sized to provide a resolution of the image formed in front of the retina that is finer than the resolution of the retina.

[0015] According to some embodiments, a device for stimulating the retina comprises microdisplays located toward the periphery of the lens away from the center of the lens, in which each microdisplay is coupled to a microlens array located behind the microdisplay. The microdisplays may comprise an array of OLEDs (organic light emitting diodes) or microLEDs. The microlens arrays are optically coupled to the displays and can efficiently collect light from the microdisplays and substantially collimate and / or focus the light before projecting the light into the entrance pupil. Images created by these displays can be myopically or hyperopically defocused and symmetrically placed in multiple regions on the retina, such as four sectors (undernasal, abovenasal, undertemporal, and abovetemporal). The microdisplays can be located away from the optical center of the lens by a distance in the range of 1.5 mm to 4.0 mm, such as 2.5 mm to 3.5 mm. The central optical zone 14 of the lens can be configured to provide normal vision for the wearer and may have a diameter in the range of 3.0 to 5.0 mm. Each microdisplay may generate a retinal image at an angle of about 20-60 degrees relative to the fovea, with a suitable shape such as circular or arcuate. In some embodiments, the retinal image is formed at a peripheral retina at an eccentricity in the range of 7.5 degrees to about 45 degrees, or 15 degrees to about 45 degrees, or 15 degrees to 40 degrees, e.g., in the range of 15-30 degrees, 20-30 degrees, or 25-30 degrees. The lens may include an electronic control system mounted with the microdisplays and other components on a flexible transparent sheet of material such as plastic.

[0016] In some embodiments, the microdisplay comprises an OLED with a pixel size in the range of 2.0 micrometers (microns) to 5.0 microns with a pitch in the range of 3.0 microns to 10.0 microns. In some embodiments, the microdisplay comprises an OLED with a pixel size in the range of 5.0 micrometers (microns) to 50.0 microns with a pitch in the range of 10.0 microns to 100.0 microns. In some embodiments, the microdisplay, which is integrated into the lens, comprises microLEDs to illuminate an object, such as a thin film placed in front of it, towards the eye. The film may be transparent or semi-transparent with a printed pattern that may be a Fourier transform of an image designed to be projected onto the retina. The microdisplay may comprise a polychromatic or monochromatic microdisplay. A polychromatic image can be formed by RGB pixels in different colored OLEDs or microLEDs organized into an array to form an RGB display. In some embodiments, the wavelength for stimulation of the retina is in the range of about 450 nm to about 560 nm (in some embodiments, about 410 nm to about 560 nm), and the peak wavelength for stimulation of the rods in the eye may be about 500 nm, although other wavelengths may be used. In some embodiments, the chromaticity of the light source includes violet light, with wavelengths in the range of 400 to 450 nm.

[0017] In some embodiments, the optical arrangement comprises one or more light sources coupled to one or more projection optics comprising one or more of a collimating lens, a compound lens such as a Gabor lens, a prism, an array of prisms, a mirror, a light guide, a waveguide, a plurality of mirrors, or a holographic mirror. In some embodiments, the waveguide is configured to preserve the phase of a wavefront transmitted therethrough. The one or more projection optics can be configured to image the one or more light sources to project an image of the light source in front of, behind, or on the peripheral retina. In some embodiments, the optical arrangement is located at or near the front surface of the lens, and light rays from the microdisplay are focused by the lens. In some embodiments, the lens is configured to provide refractive correction to the wearer, and the display optics is configured to provide an additional focus and provide a defocused image of the microdisplay on the retina. In some embodiments, the amount of defocus can be in the range of about 2.00 diopters (D) to 6.00 D, and can be in the range of about 2.0 D to 4.0 D.

[0018] In some embodiments, the spectacle lens is configured with an eyepiece display that projects a myopically defocused image of 2.0-5.0D or 2.0-7.0D to the outer retina while maintaining central vision toward the retinal periphery. In some embodiments, the device includes a pair of spectacle lenses configured with an eyepiece display that projects a pair of myopically defocused images of 2.0-5.0D or 2.0-7.0D to the retinal periphery while maintaining central vision. Each optical system of the device is coupled to an eyepiece display and may project one or more myopically defocused images to the retinal periphery while the optical center of the spectacle lens optics provides the wearer with the refractive correction required for distance vision. The optical system can be configured to provide refractive correction to enable comfortable and clear viewing of the real world at all object distances while the display projects a myopically defocused image of 2.0-5.0D or 2.0-7.0D to the outer portion of the retina.

[0019] In some embodiments, the spectacle lens is configured to project a myopically defocused image to the retinal periphery while maintaining good focus at the central retina. In some embodiments, the spectacle lens is configured to provide a bright field, in which the refractive power of the lens varies with gaze direction and object distance across the body of the spectacle lens optics. In some embodiments, the spectacle lens is configured to provide a match between vergence, image magnification, and refractive correction. In some embodiments, near vision is typically associated with lower gaze angles (downward gaze), and the refractive power of the multifocal or cumulative sum spectacle lens optics increases downward. In some embodiments, the eyeglasses are configured for a wearer who can accommodate, and the eyeglasses provide a slight + refractive power. In addition, the optical design of the binocular optics may be adjusted to encourage binocular summation while performing conjugate eye movements. In some embodiments, the area of ​​the spectacle lens optics that is left uncorrected is an area of ​​about 8-15 mm, preferably 10-12 mm in diameter, located around the optical center of the spectacle lens optics. In some embodiments, the area of ​​the spectacle lens optic that is left unmodified is an area disposed around the optical center of the spectacle lens optic, preferably with a diameter of 10-15 mm.

[0020] In some embodiments, the eyepiece display comprises a miniature light source, such as an organic light emitting diode ("OLED"), transparent organic LED ("TOLED") or i-LED, and a microlens array to substantially collimate the light emanating from the light source and direct it to the pupil of the eye. Alternatively, or in combination, a micromirror array can be used to collimate the light emanating from the light source and direct it to the pupil of the eye. In some embodiments, the light source is mounted on a transparent substrate (e.g., TOLED), while in some embodiments it may be mounted on an opaque substrate, such as silicon. The light source may comprise an active matrix or a passive matrix. The components can be held together in a transparent hermetically sealed package. In some embodiments, the hermetically sealed package may comprise a multi-layer film that is conformal and has a total thickness in the range of 5 microns to 25 microns, e.g., 10 microns to 15 microns. The device may also include a component that can monitor eye movements, such as an eye tracker. In some embodiments, the eye tracker is configured to locate a point on the eyeglass lens optics corresponding to a gaze point, which is the optical axis of the eye that intersects with the optics for a particular position of the eye, as the eye performs a tracking eye movement, such as tracking a moving object. In some embodiments, eye movements may be monitored and tracked by an eye tracker, which may comprise a coil built into the eyeglass frame that senses eye movements through the generation of a transient magnetic field, for example from the movement of a coil, such as a coil in a contact lens worn on the eye, during eye movements. In some embodiments, the retinal image formed by the light beam from the display is myopically defocused 2.0D-5.0D or 2.0-7.0D in front of the retina to form an image in front of the retina and incident on an outer portion of the retina. The image may be formed in front of the retina in many ways, but in some embodiments, the image is formed at an eccentricity of about 15 degrees to 40 degrees relative to the fovea. In some embodiments, the image is formed at an eccentricity of about 5 degrees to 40 degrees relative to the fovea. The present invention provides, for example, the following: (Item 1) 1. A device for providing stimulation to a retina of an eye, comprising: A device comprising one or more optical systems for projecting one or more images onto the retina outside the fovea to facilitate one or more of changes in axial length or choroidal thickness of the eye. (Item 2) Item 1 , wherein the one or more images comprise one or more of a still image or a dynamic image. (Item 3) 3. The device of claim 2, wherein the image comprises a dynamic image with a refresh rate in the range of 1 Hz to 200 Hz. (Item 4) Item 1. The device of item 1, wherein the one or more images comprise one or more of monochromatic or polychromatic light having wavelengths in the range of 400 nm to 800 nm. (Item 5) Item 1, the device, wherein the image has information or content in a spatial frequency range of 1 cycle / degree to 60 cycles / degree, optionally 1 cycle / degree to 10 cycles / degree. (Item 6) Item 1. The device of item 1, wherein the image has a contrast within the range of 99.9% to 2.5%. (Item 7) Item 2. The device of item 1, wherein the image has an eccentricity relative to the fovea in the range of 5 degrees to 40 degrees. (Item 8) 8. The device of claim 7, wherein the image illuminates the retina within the area with a pattern that extends substantially continuously 360 degrees around the fovea. (Item 9) 8. The device of claim 7, wherein the image illuminates a portion of the retina within the range. (Item 10) Item 1. The device of item 1, further comprising circuitry for stimulating the retina with the one or more images using transient illumination comprising one or more of continuous illumination, intermittent illumination, periodic illumination, or aperiodic illumination. (Item 11) Item 11. The device of item 10, wherein the temporary illumination comprises periodic illumination for a duration in the range of 1 second to 24 hours. (Item 12) Item 11. The device of item 10, wherein the temporary illumination comprises intermittent illumination for a duration in the range of 1 second to 24 hours. (Item 13) Item 11. The device of item 10, wherein the circuitry is configured to illuminate the retina when the subject is awake, asleep, or one or more of asleep or awake. (Item 14) Item 1, the device of item 1 further comprising circuitry for stimulating the retina with the one or more images using a spatial illumination pattern comprising one or more of a continuous spatial illumination pattern, an intermittent spatial illumination pattern, a periodic illumination pattern, or a non-periodic spatial illumination pattern. (Item 15) Item 1. The device of item 1, wherein the one or more images have a brightness in the range of 1 to 1000 Tronds. (Item 16) Item 2. The device of item 1, wherein the one or more optical systems are configured to project the one or more images with a brightness in the range of 100 to 50,000 nits or in the range of 1 to 10,000 nits. (Item 17) 2. The device of claim 1, wherein the one or more images are corrected for refractive error of the eye. (Item 18) 2. The device of claim 1, wherein the one or more images are defocused to one or more locations on the retina where the one or more images illuminate the retina. (Item 19) Item 19. The device of item 18, wherein the one or more images are myopically defocused within a range of 2.0D to 7.0D, optionally 2.0D to 5.0D. (Item 20) Item 19. The device of item 18, wherein the one or more images are hyperopically defocused by an amount in the range of 2.0D to 7.0D, optionally 2.0D to 5.0D. (Item 21) Item 1. The device of item 1, wherein the one or more optical systems comprise components of an optical projection system. (Item 22) 22. The device of claim 21, wherein the light projection system comprises one or more components of a projector, an ophthalmic device, a TV screen, a computer screen, a handheld, a mobile computing device, a tablet computing device, a smartphone, a wearable device, an eyeglass lens, an ocular display, a head mounted display, goggles, a contact lens, an implantable device, a corneal onlay, a corneal inlay, a keratoprosthesis, or an intraocular lens. (Item 23) 22. The device of claim 21, further comprising a support coupled to the projection system, the support comprising one or more of an ophthalmic device, a TV screen, a computer screen, a handheld, a mobile computing device, a tablet computing device, a smartphone, a wearable device, an eyeglass lens frame, an eyeglass lens, an eyepiece display, a head mounted display, goggles, a contact lens, an implantable device, a corneal onlay, a corneal inlay, a keratoprosthesis, or an intraocular lens. (Item 24) Equipped with a plurality of light sources, 2. The device of claim 1, wherein the one or more optical systems comprise a plurality of projection optical systems coupled to the plurality of light sources and projecting a plurality of images in front of the retina. (Item 25) 25. The device of claim 24, wherein the multiple projection optical systems are arranged to project multiple images of the multiple light sources onto multiple outer regions of the retina of the eye with an eccentricity in the range of 5 degrees to 30 degrees relative to the fovea of ​​the eye, optionally in the range of 15 degrees to 30 degrees. (Item 26) 25. The device of item 24, wherein each of the plurality of projection optical systems is arranged to project an image that is myopically defocused onto a retinal surface, the amount of defocus being in the range of 2.0D to 7.0D, optionally in the range of 2.0D to 5.0D. (Item 27) 25. The device of item 24, wherein each of the plurality of projection optical systems is located 1.5 mm to 5.0 mm from the center of the contact lens, and optionally, the plurality of projection optical systems are located along a circular circumference. (Item 28) 25. The device of claim 24, wherein the plurality of projection optical systems comprises a plurality of image forming optical systems optically coupled to the plurality of light sources and projecting the plurality of images in front of the surface of the retina. (Item 29) 30. The device of claim 28, wherein each of the plurality of light sources has a maximum transverse distance not exceeding 26 microns, optionally not greater than 10 microns, optionally wherein the maximum transverse distance constitutes a diameter. (Item 30) Item 30. The device of item 28, wherein each of the plurality of projection optical systems comprises one or more of a mirror, a lens, or a light guide. (Item 31) Item 31. The device of item 30, wherein each of the plurality of image-forming optics comprises one or more of a diffractive element, a Fresnel lens, or a compound Gabor lens. (Item 32) Item 31. The device of item 30, wherein each of the plurality of imaging optics has a maximum traversal distance in the range of 200 microns to 1.5 mm, optionally comprising a diameter. (Item 33) Item 31. The device of item 30, wherein each of the plurality of image-forming optics is aspheric and corrected for image aberrations. (Item 34) Item 31. The device of item 30, wherein each of the plurality of image-forming optics comprises a combination of convex and concave mirrors. (Item 35) Item 34. The device of item 33, wherein each of the plurality of image forming optical systems forms an image in front of an outer portion of the retina at an eccentricity within a range of 1 degree to 30 degrees from the fovea, optionally 10 degrees to 30 degrees from the fovea, optionally 15 degrees to 30 degrees, and further optionally 25 degrees to 30 degrees. (Item 36) Item 34. The device of item 33, wherein each of the plurality of image-forming optical systems creates an image in front of the retina using an image with a magnification ratio in the range of 5 to 20 or in the range of 25 to 100. (Item 37) 25. The device of item 24, wherein the anterior image of the outer portion of the retina has a modulation transfer function magnitude of 0.75 or greater at a spatial frequency of 10 lp / mm, 0.40 or greater at a spatial frequency of 30 lp / mm, optionally 0.75 or greater at a spatial frequency of 10 lp / mm, 0.40 or greater at a spatial frequency of 50 lp / mm. (Item 38) Item 31. The device of item 30, wherein each of the plurality of projection optical systems comprises an image forming optical system comprising a collimating optical system configured to form the image in front of the retina. (Item 39) 31. The device of claim 30, wherein the projection optics comprises a single lens for functioning as both a collimating optics and an image forming optics. (Item 40) Item 31. The device of item 30, wherein the projection optics comprises image forming optics for creating an image in front of the outer portion of the retina with an eccentricity of 30 degrees or less and a depth of focus of 1.0D or less. (Item 41) 40. The device of claim 39, wherein the optical system creates the image in front of an outer portion of the retina with an eccentricity of 30 degrees or less, and the modulation transfer function of the image decreases by a minimum of 0.1 units for 1.0D of defocus, optionally, the 1.0D of defocus constituting an incremental defocus. (Item 42) Item 25. The device of item 24, wherein the multiple light sources comprise multiple microdisplays. (Item 43) Item 25. The device of item 24, wherein the plurality of light sources comprises a plurality of light emitting diodes (LEDs). (Item 44) 25. The device of claim 24, wherein each of the plurality of optical elements comprises a mirror assembly that collimates light emitted by a corresponding microdisplay and directs the resulting light beam into the pupil of the eye, where the light beam is focused to form the peripheral image in front of the retina. (Item 45) 25. The device of claim 24, wherein each of the plurality of optical elements comprises a lens that receives light emitted by a corresponding microdisplay and directs the resulting light beam into the pupil of the eye, where the light beam is focused to form an image in front of the retina. (Item 46) Item 25. The device of item 24, wherein the multiple light sources generate polychromatic illumination, and optionally the multiple light sources comprise multiple microdisplays that generate polychromatic illumination. (Item 47) 25. The device of claim 24, wherein the image is about 0.5 mm to 2.0 mm in front of the retina. (Item 48) 25. The device of item 24, wherein the image has a resolution of at least 10 lp / mm, optionally at least 30 lp / mm. (Item 49) 25. The device of claim 24, wherein the image has a magnification of 200x or less, optionally 100x or less. (Item 50) Item 25. The device of item 24, wherein the image has a depth of focus of 2.5 diopters or less, optionally the depth of focus is about 0.9 mm or less. (Item 51) Item 25. The device of item 24, wherein the image is projected at an eccentricity in the range of about 7.5 degrees to about 45 degrees, optionally in the range of about 15 degrees to about 45 degrees. (Item 52) Item 52. The device of item 51, wherein the range is from about 15 degrees to about 30 degrees. (Item 53) The microdisplay has a resolution of about 100 cd / m 2 ~50,000cd / m 2 in the range of about 0.1 cd / m2 ~10cd / m 2 25. The device of claim 24, wherein the pupil is illuminated with an illuminance in the range of (Item 54) 25. The device of claim 24, wherein the image is focused at a distance in front of the peripheral retina at a location, the image having a depth of focus and a spatial resolution, the depth of focus being less than the distance and the spatial resolution exceeding the spatial resolution of the peripheral retina at the location. (Item 55) Item 25. The device of item 24, further comprising a sensor for receiving input from the wearer when the contact lens is placed on the wearer's eye. (Item 56) 1. A spectacle lens comprising a display, the display projecting an image onto the periphery of the retina to reduce the progression of myopia. (Item 57) Item 58. The eyeglass lens of item 56, wherein the display comprises a microdisplay. Item 57. The eyeglass lens of item 56, wherein the display comprises a picoprojector coupled to the eyeglass frame at a location corresponding to the wearer's temples. (Item 59) Item 57. The eyeglass lens of item 56, wherein the display comprises an eyepiece display. (Item 60) Item 57. The eyeglass lens of item 56, wherein the display is configured to stimulate ingrowth of the retina. (Item 61) Item 57. The eyeglass lens of item 56, wherein the display comprises a microdisplay and a micro-optical array. (Item 62) 57. The eyeglass lens of item 56, wherein the display enables clear viewing of the real world over a field of view within a range of + / - 2.0 degrees to + / - 15 degrees, optionally within a range of about + / - 2.0 degrees to + / - 12.5 degrees. (Item 63) Item 62. The eyeglass lens of item 61, wherein the display projects an image of the light source of the microdisplay that is myopically defocused by an amount in the range of 2.0D to 7.0D, optionally in the range of 2.0D to 5.0D. (Item 64) Item 57. The eyeglass lens of item 56, wherein the display projects an image onto the outer region of the retina at an eccentricity relative to the fovea in the range of 15 degrees to 40 degrees, optionally in the range of 20 degrees to 30 degrees. (Item 65) Item 57. The eyeglass lens of item 56, wherein the lens comprises multiple ocular displays to enable binocular stimulation of the outer retina. (Item 66) 57. The spectacle lens of item 56, wherein the display transmits more than 80% of the light incident thereon over a field of view of + / - 5 degrees or more to the side and + / - 7 degrees vertically, optionally + / - 12 degrees or more to the side and + / - 20 degrees vertically. (Item 67) 2. The eyeglass lens or device of claim 1, wherein the projected image moves to compensate for eye movement, and optionally the projected image moves to provide stimulation to overlapping regions of the periphery of the retina in response to eye movement. (Item 68) 2. The eyeglass lens or device of any one of the preceding claims, wherein the periphery of the retina constitutes an outer location of the retina, located away from the macula. (Item 69) 13. The device of any one of the preceding claims, further comprising a processor coupled to the plurality of light sources and configured to control illumination of the plurality of light sources. (Item 70) 2. The device of any one of the preceding claims, further comprising wireless communication circuitry operatively coupled to the plurality of light sources and configured to control illumination of the plurality of light sources. (Item 71) 2. The device of claim 1, further comprising wireless communications circuitry operably coupled to a mobile device for the wearer to control illumination of the plurality of light sources. (Item 72) 2. The device of any one of the preceding claims, further comprising wireless communication circuitry operably coupled to the processor for a health care provider to program illumination cycles and intensities of the plurality of light sources. (Item 73) 7. The device of any one of the preceding claims, wherein the device does not include a contact lens. [Brief description of the drawings]

[0021] A better understanding of the features, advantages, and principles of the present disclosure will be obtained by reference to the following detailed description that sets forth illustrative embodiments and the accompanying drawings.

[0022] [Figure 1] FIG. 1 illustrates a soft contact lens according to some embodiments.

[0023] [Figure 1A] 1A and 1B show eyeglasses suitable for incorporation with the present disclosure, according to some embodiments. [Figure 1B] 1A and 1B show eyeglasses suitable for incorporation with the present disclosure, according to some embodiments.

[0024] [Figure 2A] FIG. 2A shows an OLED microdisplay integrated into a soft contact lens and optically coupled with a microlens array to project an image with myopic defocus onto the periphery of the wearer's retina, according to some embodiments.

[0025] [Figure 2B] FIG. 2B illustrates a soft contact lens with multiple light sources and optical systems and associated circuitry according to some embodiments.

[0026] [Figure 2C]FIG. 2C shows a functional diagram of the components of a contact lens as in FIG. 2B.

[0027] [Diagram 3] FIG. 3 shows an optical configuration in which the optical path length is increased by folding the optical path using two mirrors, according to some embodiments.

[0028] [Figure 4] FIG. 4 shows a ray tracing simulation of the optical configuration shown in FIG. 3 in which the Liou Brennan eye model is used to calculate the retinal image, according to some embodiments.

[0029] [Diagram 5] 5A and 5B show an analysis of the retinal image quality produced by the optical configuration of FIG.

[0030] [Figure 6] FIG. 6 shows an analysis of the depth of focus of the optical configuration shown in FIG.

[0031] [Figure 7] FIG. 7 shows the MTF for the analysis of FIG.

[0032] [Figure 8] 8A and 8B show an optical configuration comprising a lens for focusing light onto the retina, according to some embodiments.

[0033] [Figure 9] FIG. 9 shows an analysis of the retinal image quality produced by the optical configuration shown in FIGS. 8A and 8B, according to some embodiments.

[0034] [Figure 10] FIG. 10 shows an analysis of the depth of focus of the optical configuration shown in FIGS. 8A and 8B.

[0035] [Figure 11] 11A and 11B show a light pipe for increasing the optical path length, according to some embodiments.

[0036] [Figure 12] FIG. 12 shows a soft contact lens with built-in light source, optics, and electronics, according to some embodiments.

[0037] [Figure 13] FIG. 13 shows a ray tracing simulation of a peripheral retinal image formed by a combination of a miniature light source and micro-optics according to some embodiments.

[0038] [Figure 14] FIG. 14 shows four object points used to simulate image quality using ray tracing for a light source with four simulated object points, according to some embodiments.

[0039] [Figure 15] FIG. 15 illustrates the quality of a peripheral image produced by a reflective optical system in which the modulation transfer functions (MTFs) of all object points are substantially matched, according to some embodiments.

[0040] [Figure 16] FIG. 16 illustrates the depth of focus of a peripheral image formed by a reflective optical system, according to some embodiments.

[0041] [Figure 17] FIG. 17 shows the effect of myopic blur on image resolution of peripheral retinal images formed by reflective optics, as measured by the change in magnitude of the MTF at a single spatial frequency (20 / 200 or 10 line pairs / mm “lp / mm” or 10 arc minutes) as a function of the magnitude of myopic defocus for a reflective optical design, according to some embodiments.

[0042] [Figure 18]FIG. 18 shows MTF plots of retinal images formed by a refractive optical system for the four object points shown in FIG. 14, according to some embodiments.

[0043] [Figure 19] FIG. 19 illustrates the depth of focus of an image formed by a refractive optical system, according to some embodiments.

[0044] [Figure 20] FIG. 20 shows the calculated MTF for a single spatial frequency (20 / 200 or 10 lp / mm or 10 arc minutes) as a function of myopic defocus according to some embodiments.

[0045] [Figure 21] FIG. 21 shows MTF plots of the four object points in FIG. 14 for an embodiment with a compact light guide in which there is a substantial difference in image quality between the sagittal and tangential planes, exhibiting asymmetric aberrations in accordance with some embodiments.

[0046] [Figure 22] FIG. 22 shows the depth of focus of a peripheral retinal image projected by the light guide optics, according to some embodiments.

[0047] [Figure 23] FIG. 23 shows an MTF plot at a single spatial frequency (20 / 200) plotted against the magnitude of myopic defocus of the peripheral image on the retina for an embodiment with a light guide.

[0048] [Figure 24] FIG. 24 shows a comparison of depth focus of peripheral images produced by three projection systems comprising refractive optics, reflective optics, and light guide optics, according to some embodiments.

[0049] [Diagram 25]FIG. 25 shows the depth of focus of a retinal image produced by a reflective optics design, according to some embodiments.

[0050] [Figure 26] FIG. 26 shows MTF values ​​at a single spatial frequency plotted against the magnitude of myopic defocus for a peripheral image produced by the reflective optics design of FIG. 25, according to some embodiments. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0051] (Detailed Description) The method and device of the present disclosure can be configured in many ways to provide retinal stimulation as described herein.The method and device of the present disclosure are highly suitable for combination with many previous devices, such as one or more of ophthalmic devices, TV screens, computer screens, handhelds, mobile computing devices, tablet computing devices, smartphones, wearable devices, eyeglass lens frames, eyeglass lenses, eyepiece displays, head-mounted displays, goggles, contact lenses, implantable devices, corneal onlays, corneal inlays, keratoprostheses, or intraocular lenses.Although specific reference is made to eyeglasses and contact lenses, the method and device of the present disclosure are highly suitable for use with any of the aforementioned devices, and those skilled in the art will easily understand how one or more of the components of the present disclosure can be interchanged between devices based on the teachings provided herein. For example, specific reference is made to contact lenses with projection optics, light sources, and circuitry to stimulate the retina away from the fovea, but the projection optics, light sources, and circuitry can be incorporated into one or more of an ophthalmic device, a TV screen, a computer screen, a handheld, a mobile computing device, a tablet computing device, a smart phone, a wearable device, an eyeglass lens frame, an eyeglass lens, an ocular display, a head mounted display, goggles, a contact lens, an implantable device, a corneal onlay, a corneal inlay, a keratoprosthesis, or an intraocular lens to provide retinal stimulation as disclosed herein.

[0052] The methods and devices for retinal stimulation as described herein can be configured in many ways and may include one or more attributes to prompt a user to undergo therapy. For example, retinal stimulation as described herein can be combined with the display of a game to prompt a user to wear a therapeutic device. In some embodiments, retinal stimulation can be combined with another stimulus, such as an emoji, to prompt a user to wear a therapeutic device.

[0053] The retinal stimulation device may include global positioning system (GPS) circuitry for determining the wearer's location and an accelerometer for measuring body movements such as head movement. The retinal stimulation device may include a processor coupled to one or more of the GPS or accelerometer to receive and store measured data. The retinal stimulation device may include communication circuitry such as wireless communication circuitry, e.g., Bluetooth or WiFi, or wired communication circuitry, e.g., USB, for transmitting data from the device to a remote server, such as a cloud-based data storage system. This transmission of data to a remote server can allow the wearer's treatment and compliance to be monitored remotely. In some embodiments, the processor includes a graphics processing unit (GPU). The GPU can be used to efficiently and rapidly process content from the web in order to utilize this content in forming the stimuli as described herein.

[0054] In some embodiments, the device includes one or more cameras capable of capturing still or video images of real-world scenes that can be used to form a stimulus signal.

[0055] In some embodiments, the one or more projection optics are configured to project a defocused image onto the retina away from a central field, including the macula, to stimulate an increase in choroidal thickness. In some embodiments, the one or more projection optics are configured to project a defocused image onto the retina away from a central field, including the macula, to stimulate a transient increase in choroidal thickness. The one or more projection optics can be configured to stimulate the retina without degrading central vision and corresponding images formed on one or more of the foveal or macular regions of the retina. In some embodiments, the one or more projection optics do not reduce the image forming characteristics of a vision correction optics prescribed to correct the wearer's refractive error. The correction optics may comprise one or more of a contact lens, a spectacle lens, an intraocular lens, a corneal onlay, or a corneal inlay. The one or more projection optics can be coupled to one or more light sources to illuminate the retina with one or more defocused images. In some embodiments, the one or more light sources comprise an optical display, such as a micro-optical display, and the one or more projection optics comprise a micro-optical array. The components are mounted on a flexible printed circuit board ("PCB") substrate, which can support electronic and optical components. In some embodiments, the microdisplay is optically coupled to a micro-optic array that substantially collimates and focuses light emanating from the microdisplay. The microdisplays may each comprise small pixels with sizes in the range of 2 microns to 100 microns. The microdisplay can be coupled to and supported by a body of corrective optics, such as, for example, a contact lens or a spectacle lens. In some embodiments, the microdisplay is coupled to and supported by one or more of an intraocular lens, a keratoprosthesis, a corneal onlay, or a corneal inlay. The optical configurations described herein with reference to a contact lens can also be used with, for example, one or more of an intraocular lens, a keratoprosthesis, a corneal onlay, or a corneal inlay.

[0056] In some embodiments, the one or more projection optics are coupled to and supported by a pair of eyeglasses. For example, the projection optics can be coupled to or built into the outer surface of a pair of eyeglass lenses. In some embodiments, the projection optics comprises a picoprojector mounted on the temples of the eyeglass frames. In some embodiments, the projection optics is optically coupled to one or more optical fibers that deliver the projected image to the eyeglass optics and direct it to the pupil of the eye, for example, using a partially transparent mirror. In these embodiments, the eye tracker can be configured to monitor eye movements such that activation of pixels in the microdisplay can be programmed to compensate for eye movements recorded by the eye tracker. In some embodiments, the eye tracker comprises a search coil mounted in the inner surface of the frame of the eyeglass lenses. The search coil can be configured to detect eye movements in a number of ways. In some embodiments, the subject wears a contact lens to provide refractive correction for the subject's eye. A metal wire or magnetic material is built into the contact lens that creates a magnetic field in the search coil when eye movements occur. In some embodiments, the magnetic field is analyzed with a processor to determine eye start and stop points and the time it takes to perform the eye movement. In some embodiments, the microdisplay and circuitry coupled to the display are configured to respond to the eye movement and selectively activate a different plurality of pixels within an appropriate time in response to the eye movement. The time to selectively switch to a second plurality of pixels in response to the eye movement can be less than 100 milliseconds, for example, less than 20 milliseconds.

[0057] In some embodiments, the microdisplay and the micro-optic array are mounted immediately adjacent to each other on the same corrective optic, separated by a fixed distance, to project a bundle of light rays to the pupil of the eye in an orientation that forms a myopically defocused image at a desired location on the retina, as described herein. In some embodiments, the one or more projection optics are mounted on or within the one or more corrective optics such that light rays from the projection optics are refracted through the corrective optics. The corrective optics refract the light rays from the projection optics to be convergent or divergent, as is useful for emmetropia, such that the micro-optic array can provide a desired amount of additional refractive power, which can be + or - depending on the magnitude and sign of the desired defocus. The microdisplay may be, for example, monochromatic or polychromatic. The microdisplay may have a brightness, for example, in the range of 1 nit to 10,000 nits, or 10 nit to 1000 nits, or 100 lux to 5,000 lux. In some embodiments, the microdisplay may have a brightness in the range of, for example, 100 nits to 50,000 nits or 50 lux to 5,000 lux. In some embodiments, the microdisplay is positioned off-center relative to the optical center of the correction optics at a distance in the range of 1.0 mm to 4.0 mm from the center of the correction optics. In some embodiments, the microdisplay forms an extended array of pixels characterized by a pixel size and a pixel pitch, in which the pixel size and pixel pitch together correspond to a fill factor of the microdisplay. As described herein, the pixel size may range from 2 microns to 100 microns, and the pixel pitch may range from, for example, 10 microns to 1.0 mm. The corresponding fill factor can range from 0.1% to 10%. In some embodiments, the pixel array is optically coupled with the micro-optic array to substantially collimate and focus light from the pixels. In some embodiments, the layers of the microdisplay and the layers of the micro-optic array are encapsulated in a substantially transparent medium configured to reduce light scattering.The encapsulated image delivery system, including one or more light sources and one or more projection optics, may, for example, then be coated with a conformal, hermetically sealing transparent multi-layer coating.

[0058] In some embodiments, the microdisplay may be mounted on a corrective optic such as a spectacle lens, while the micro-optic array may be mounted on a second corrective optic such as a contact lens, corneal onlay, or corneal inlay. Alternatively, or in combination, an augmented reality (AR) or virtual reality (VR) display may be used to project the defocused image onto the retina. The AR or VR device may be mounted on a spectacle frame, goggles, or head-mounted display. Refractive correction may be provided by the spectacle lens or contact lens, while an optic coupled to the micro-optic array of the AR or VR device provides the defocus.

[0059] In some embodiments, the projected defocused image may be provided by a screen, comprising one or more of an LCD screen, an OLED (organic light emitting diode), a TOLED, an AMOLED, a PMOLED, or a QLED-driven screen. The screen may appear to the subject at a long distance, for example, of at least 6 meters or more.

[0060] The stimuli can be configured in many ways and may comprise monocular or binocular stimuli.

[0061] The micro-optical array can be configured in many ways and may comprise one or more of an array of lenslets, an array of compound lenses such as Gabor lenses, one or more mirrors, a prism, a light pipe or light guide, or a waveguide.

[0062] In some embodiments, the projected image comprises image structure content configured to provide a range of spatial frequencies, for example, within a range of 2 cycles / degree to about 60 cycles / degree. In some embodiments, the projected image comprises image structure content configured to provide a range of spatial frequencies, for example, within a range of 2 cycles / degree to about 30 cycles / degree. Writings related to this disclosure suggest that the peripheral retina's ability to detect blur is higher than its ability to resolve images. The size and shape of the projected image may be within a range of 100 microns to 2.5 mm, for example, for a range of angles from 15 degrees to 360 degrees or 5 degrees to 360 degrees relative to the fovea. The location of the image may be within a range of eccentricity, for example, from 5 degrees to 30 degrees, for example, within a range of 12 degrees to 30 degrees, relative to the fovea. Alternatively, the projected image may cover the entire retina for pan-retinal treatment of defocus.

[0063] In some embodiments, the brightness of the projected image is in the range of 1 Troland to 250 Troland. In some embodiments, the image brightness is adjustable based on the brightness of the ambient lighting. The contrast range of the projected image can be in the range of 99.9% to 2.5%, for example in the range of 99.9% to 10%.

[0064] The projection of the defocused image as described herein may be sustained for any suitable amount of time, for example, for a substantial portion of a day (e.g., 8 hours or more), and the stimulation may be repeated daily at approximately the same time so as not to interfere with circadian rhythms. The projected image may have a duration as short as 15 minutes, for example, repeated throughout the entire day every hour. The projected image may be sustained for a time ranging from 15 minutes to 12 hours per day. The stimulation may be provided over a cycle of one day to three years, or for as long as the treatment is beneficial.

[0065] According to some embodiments, the soft contact lenses each comprise a peripheral microdisplay, with a microlens array covering the anterior surface on the eye side. The microdisplay may comprise an array of OLEDs (organic light-emitting diodes) or microLEDs. The light emitted by these displays is typically Lambertian reflection. The microlens arrays are optically coupled with the displays such that they can efficiently extract the light from the microdisplays and collimate and focus it before projecting them into the entrance pupil. The virtual images created by these displays will in some embodiments be myopically defocused and symmetrically placed in four sectors (undernasal, abovenasal, undertemporal, and abovetemporal). The microdisplays will be located such that they are away from the optical center of the lens by a distance in the range of 1.5 mm to 4.0 mm, preferably 2.5 mm to 3.5 mm, in some embodiments. The central optics of the contact lens can be selected to bring the wearer as close to emmetropia as possible and may have a diameter in the range of 3.0 to 5.0 mm. Each microdisplay, in some embodiments, is circular, rectangular, or arcuate in shape, each having a resolution of less than 0.01 mm 2 ~8.0mm 2 Within the range of, for example, 0.04 mm 2 ~8.0mm 2 Within the range of, for example, 1 mm 2 ~8mm 2 or preferably within 1.0 mm 2 ~4.0mm 2In some embodiments, each of the multiple microdisplays comprises a light source, a back surface, and associated electronics with dimensions and shapes as described herein. The contact lens will have an electronic control system and a microdisplay mounted on a flexible transparent sheet of plastic. The electronic system may comprise an ASIC or microcontroller, a rechargeable lithium ion solid state battery, a voltage ramp module, e.g., a buck-boost converter, flash memory and EEPROM, an RFID module to provide wireless recharging, or an antenna preferably radially disposed along the edge of the contact lens, and any combination thereof. The contact lens may comprise any material composition that is made of a biocompatible material, such as a soft hydrogel or silicone hydrogel material, and has been proven to be compatible with sustained wear on the eye as a contact lens.

[0066] In some embodiments, the virtual images are focused at a target distance from the peripheral retina, which corresponds to myopic defocus. The light rays forming these images originate from the microdisplays themselves, not from the outside environment, and therefore the optics of the microlens array can be designed only to process the light rays emanating from the microdisplays. The area of ​​each of these microdisplays and the microlens array in front of each one is small, as shown in Figures 1 and 2, and therefore the obscuration of the real image is also small.

[0067] Devices as described herein give each treatment provider substantial flexibility in setting and testing such parameters for an individual patient and can then refine the preferred parameters of treatment based on observation of the patient response.

[0068] Some embodiments comprise a contact lens with a diameter of 14.0 mm, with a 1.0 mm edge zone and a peripheral zone 16 whose inner diameter is 6.0 mm and outer diameter is 12.0 mm. The overall diameter of the lens may be in the range of 13.0 mm to 14.5 mm, preferably 13.5 to 14.5 mm. The central optic zone 14 is designed to cover all wearer pupils under all lighting conditions and should therefore have a diameter in the range of 5.0 mm to 8.0 mm. The peripheral or blend zone is primarily designed to provide a good fit with the cornea, including good centration and minimal deviation. The central optic zone 14 is designed to provide the wearer with emmetropia correction and may be provided with both spherical and astigmatic correction (FIG. 1). Contact lens designs suitable for incorporation with the embodiments disclosed herein are described in Douthwaite, DA, “Contact lens optics and lens design”, 3 rd edition, 2006; ISBN978-0-7506-88-79-6; Explained in Butterworth-Heinemann.

[0069] In some embodiments, the inner surface of the contact lens is built with a set of four microdisplays bonded to the eye side with an identically sized microlens array. The function of the microlens array is to collimate the light emitted by the microdisplays and focus it to a focal point designed to be in front of the eye to provide hyperopic defocus. The microdisplays can be sized in many ways, and each of these microdisplays is sized in some embodiments to be only about 0.04 mm, so that these displays cover less than 1% of the contact lens optics. 2 ~2mm 2 Area of, for example, 1 mm 2 ~2mm 2 Each of these displays has an area of ​​approximately 30-50 cd / m, which is quite enough to form a relatively bright image at the focal point of each of these microdisplays. 2The focused image would appear approximately 1.5 to 2.5 mm in front of the peripheral retina, as they would be designed to be, for example, approximately 2.0D to 5.0D, e.g., 2.0D to 4.0D, or preferably, 2.5D to 3.5D myopic.

[0070] In some embodiments, the microdisplay may be an OLED with a pixel size of 2.0 microns to 5.0 microns with a pitch in the range of 2.0 microns to 10.0 microns. In some embodiments, the microdisplay built into the contact lens as described herein will consist of a microLED that illuminates an object such as a thin film placed in front of it, i.e., on the eye side. The microdisplays may be polychromatic or they may be monochromatic. Polychromatic images are formed by RGB pixels in the OLED or microLED of different colors that are organized in an array to form an RGB display. There is a lack of data on the wavelength dependence of axial length alteration of hyperopic or myopic images projected onto the peripheral retina. The preferred wavelength for stimulation of axial length change is 500 nm, which is the peak wavelength for stimulation of rods in the eye, but other wavelengths may also be used.

[0071] The amount and location of illumination on the outer retina to provide therapeutic benefits can be determined by those skilled in the art without undue experimentation, following the teachings disclosed herein. The length and duration of peripheral stimulation can be determined, e.g., optimized, based on available preclinical data in animal models. For example, some studies suggest that axial length changes in animal models can be obtained in repeated applications of defocus stimulation, rather than a single sustained cycle of equivalent duration of imposed defocus. Examples of studies with information regarding illumination changes in axial length suitable for incorporation by embodiments disclosed herein include Wallman, J., et al, "Homeostatis of eye growth and the question of myopia", in Neuron, 2004;43:pp447; Benavente-Perez, A, et al, "Axial Eye Growth and Refractive Error Development Can Be Modified by Exposing the Peripheral Retina to Relative Myopic or Hyperopic Defocus"In IOVS2014;55:pp6767; and Hammond, DS, et al, "Dynamics of active emmetropisation in young chicks-influence of sign and magnitude of imposed defocus"in Ophthalmic Physiol Opt.2013;33:pp215-222.

[0072] The writings related to this disclosure suggest that the duration and distribution of peripheral myopic defocus application will depend on the individual's physiology and the precise shape of the retina. An embodiment includes a reprogrammable MCU or ASIC that controls the operation of the microdisplay and a real-time clock that will enable the treatment provider to adjust the treatment duration and periodicity throughout the treatment. This embodiment also enables the treatment provider to test whether nocturnal stimulation (sustained or repeated sequences of short pulses) has efficacy for a given individual.

[0073] In some embodiments, the electronic components are incorporated onto a flexible thin film onto which the interconnects and electrical buses are deposited using evaporation or 3D printing processes. In some embodiments, the electronics and microdisplays are further fabricated using a 5-10 micron total thickness of Paralyne C and SiO 2 developed by Coat-X, a company based in Neuchatel, Switzerland. x The barrier film is coated with a flexible stack of thin barrier films, such as a stack of films.

[0074] Some embodiments of the device deploy a set of one to eight microdisplays, each of which is circular or arc-shaped, arranged radially on the inner surface of the contact lens and all at the same distance from the optical center of the lens. In one embodiment, they may be monochromatic. In another embodiment, they may be designed to provide a white light output. In a third embodiment, they may be designed to output illumination that is matched to retinal sensitivity. These microdisplays are operated and controlled by a reprogrammable microcontroller (MCU) or ASIC.

[0075] In some embodiments, the contact lenses are worn during sleep and the microdisplay is programmed to operate only when the wearer is asleep. Such programmed stimulation of axial length reduction would only minimally interfere with daily activities, including reading and computer work. The contact lenses may even be removed during daytime activities and worn on the cornea just prior to falling asleep. Other embodiments may utilize other programming algorithms, for example, a combination of daytime and nighttime stimulation.

[0076] In some embodiments, the contact lenses may be daily disposable lenses, eliminating the need to disinfect and clean the lenses or recharge them. Another embodiment consists of planned replacement modality contact lenses.

[0077] In some embodiments, each microdisplay (1 mm 2 ~4mm 2 ) would consume about 10 microwatts of electrical energy. In these embodiments, a set of four microdisplays can use about 125 microwatt-hours of electricity over two hours of operation, such that the total daily energy consumption for this design would be expected to be 0.2 milliwatt-hours. In some embodiments, each microdisplay has a resolution of about 0.04 mm 2 ~4mm 2and consumes approximately 10 microwatts of electrical energy. In some embodiments, power is provided by a rechargeable solid-state lithium-ion battery. A bare-die solid-state rechargeable lithium-ion battery, commercially available from Cymbet Corporation, may be incorporated on the same flexible substrate as the lens electronics. For example, a 50 uAH rechargeable lithium-ion solid-film battery has dimensions of 5.7×6.1 mm×0.200 mm (Cymbet Corporation CBC050). In some embodiments, the battery provides sufficient mass to stabilize the contact lens. For example, the battery can be located on a lower position of the lens to stabilize the lens with gravity. The lower-positioned battery may provide sufficient mass to reduce rotational movement, such as spinning, when the wearer blinks.

[0078] In some embodiments, the electronic contact lens projects a myopically defocused image of 2.0-5.0D or 2.0-7.0D to the retinal periphery while maintaining excellent vision in the center.

[0079] In some embodiments, the electronic soft contact lens comprises a miniature light source and micro-scale optics integrated into the periphery of the lens optics. The contact lens optics can be designed to provide excellent vision in the central retina, while the outer light source projects an image that is myopically defocused onto the outer portion of the retina. In some embodiments, the light source comprises a microdisplay. In some embodiments, the outer image formed in front of the retina can stimulate the retina to move anteriorly, reduce its axial length, and deepen the vitreous compartment. In some embodiments, the contact lens is configured to reduce, substantially stop, or reverse myopia deterioration in an eye wearing the lens. In some embodiments, the contact lens is configured for extended wear, and can be replaced, for example, monthly. The contact lens can be replaced more frequently or less frequently, for example, weekly or once every three months. In some embodiments, the contact lens is designed to be worn by teenagers and young adults, who may be at greater risk of myopic deterioration than people of other ages.

[0080] In some embodiments, the amount of myopic defocus of the peripheral image is in the range of about 2.0D to about 7.0D, e.g., 2.0D to about 5.0D or about 2.5D to about 5D. Based on the teachings disclosed herein, one of skill in the art can conduct studies, such as clinical studies, to determine the appropriate amount of defocus, illumination intensity, and time of illumination. In some embodiments, one or more of the amount of defocus, retinal location of retinal illumination, or time of illumination can be customized to an individual, e.g., in response to the physiological characteristics of an individual patient. The duration of treatment can be in the range of 1 to 3 years, e.g., about 2 years. In some embodiments, the treatment is performed with a number of lenses in the range of about 10 lenses to about 40 lenses, e.g., about 10 lenses to about 30 lenses. The prescription of the optical zone 14, which comprises the central lens optics, can change over time during treatment, and the contact lens prescription can be changed as appropriate. Contact lenses as disclosed herein may also be worn thereafter as needed, for example, if myopia deterioration returns.

[0081] Electronic contact lenses can be configured to correct the wearer's refractive error in a number of ways. In some embodiments, the contact lens comprises a number of micro-displays that emit light near the periphery of the optical zone 14 of the contact lens, a number of micro-optics for collecting, collimating, and focusing light rays emanating from the light source, a small rechargeable solid-state battery (e.g., a lithium-ion solid-state battery) for providing power to the light source, an antenna for wirelessly receiving power and recharging the battery, a microcontroller for controlling the operating and control functions, and a memory for storing data or software instructions.

[0082] In some embodiments, the outer image comprises a peripheral image located outside the macula, for example within a range of eccentricity of about 20 degrees to about 30 degrees relative to the fovea.

[0083] Contact lenses can be configured in many ways with multiple optics, such as micro-optics, to collect light from multiple light sources (e.g., miniature light sources) and form an image in front of an outer portion of the retina, such as in front of a peripheral portion of the retina. In some embodiments, the multiple optics comprise one or more of a light pipe and a reflective component, such as a mirror, e.g., a miniature mirror.

[0084] Devices as described herein can be used to treat progression of refractive errors such as myopia, In some embodiments, each treatment provider has substantial flexibility in setting and testing parameters for an individual patient, and then refines the preferred parameters of the treatment based on observation of the patient response.

[0085] In some embodiments, the optical design of the refractive nature of the contact lens is substantially unchanged and can be configured in many ways. For example, the central optical zone 14 of the contact lens can be optimized for best correction of the far vision image at the fovea while providing an image to the periphery of the retina in front of the image shell of the contact lens optics to reduce progression of refractive error. In some embodiments, the light source is 2 mm 2 and the size of the optical surface for correcting refractive error is about 25 mm 2 ~ approx. 50mm 2 The intensity of the peripheral image, which can be provided independent of the level of ambient illumination and the intensity of the light source, can be adjusted over several orders of magnitude by selecting a light source of appropriate refractive power. Soft contact lenses can be configured to provide the appropriate amount of illumination response to input from the wearer or health care provider.

[0086] 1 shows a microdisplay 12 integrated into a lens as described herein, such as a contact lens 10. Although reference is made to a contact lens, the lens 10 may comprise one or more of a projector, an ophthalmic instrument, a TV screen, a computer screen, a handheld device such as a smart phone, a wearable device such as a spectacle lens, an ocular display, a head mounted display, goggles, a contact lens, a corneal onlay, a corneal inlay, a keratoprosthesis, or an intraocular lens.

[0087] The soft contact lens 10 comprises an optical zone 14 configured to provide the wearer with distance vision correction, e.g., with visual acuity of 20 / 20 or better. The optical zone 14 may comprise a traverse distance, such as a diameter or radius 15, which may comprise any suitable size, such as a radius of about 3 mm. The microdisplay 12 may be configured to provide an image in front of a peripheral portion of the retina, as described herein. This configuration may allow the user to have good vision while receiving therapy from an image focused in front of the retina, as described herein. The microdisplay 12 may be located outside the optical zone 14 or inside the optical zone 14. The microdisplays 12 may each comprise a maximum traverse distance, such as a diameter 19, which may comprise any suitable size, e.g., about 1 mm.

[0088] The microdisplay 12 may comprise micro LEDs that illuminate an object, such as a thin film, placed in front of it, i.e., on the eye side. The light emitted by these microdisplays 12 may be Lambertian reflection and directed to an optical element, such as a lens, to direct the light beam towards the retina. The contact lens 10 has a diameter 13 suitable for placement on the eye. For example, the contact lens 10 may have a diameter in the range of about 10 mm to 15 mm, e.g., 14.0 mm. The contact lens 10 may comprise multiple built-in microdisplays 12. Each of the multiple microdisplays 12 may be optically coupled to an optical arrangement that collects the light emitted by the microdisplay 12 and projects an image on or in front of the wearer's retina at a defined eccentricity. Each of the displays 12 may have a resolution of about 1 cd / m 2 ~about 50cd / m 2 In some embodiments, the displays 12 can each produce illumination within a range of about 50 cd / m 2 ~About 50,000cd / m 2 or about 100 cd / m 2 ~About 50,000cd / m 2 The amount of illumination may be sufficient to form a relatively bright image at the focal point of each of these microdisplays 12.

[0089] In some embodiments, the amount of illuminance is intermediate between photopic and mesopic levels of illumination and intermediate between the levels of rod and cone sensitivity. In some embodiments, the amount of illumination is greater than or equal to 100 cd / m at the pupil plane. 2 ~About 50,000cd / m 2 , preferably 10 cd / m 2 ~2000cd / m 2 etc., about 10 cd / m 2 ~About 50,000cd / m 2 In some embodiments, the amount of illumination is in the range of about 0.1 cd / m at the pupil plane. 2 ~about 10cd / m 2 , e.g., 0.5 cd / m 2 ~5cd / m2 The amount of illuminance may correspond to an amount of light between moonlight and indoor lighting, for example. In some embodiments, the amount of illumination corresponds to mesopic vision.

[0090] In some embodiments, the microdisplay 12 can include a light source that emits polychromatic light, which is made up of different wavelengths of light. In other embodiments, the light source emits monochromatic light. In some embodiments, the wavelength of the monochromatic illumination can be in the range of 500 nm to 560 nm, preferably 500 nm to 530 nm, and more preferably 500 nm to 510 nm.

[0091] In some embodiments, the polychromatic light source provides chromatic cues to the peripheral retina. The chromatic cues may comprise negative chromatic aberration. In some embodiments, a polychromatic light beam is focused in front of the retina, where the polychromatic light beam has positive chromatic aberration before the image plane 35 or focal plane, or negative chromatic aberration after the image plane 35 or focal plane, so as to illuminate the retina with negative chromatic aberration.

[0092] The polychromatic illumination can be configured in many ways, and in some embodiments the polychromatic illumination comprises red, blue, and green illumination, although other wavelengths of light may also be used.

[0093] In some embodiments, the projected images will appear about 1.5 mm to about 2.5 mm in front of the peripheral retina, as they will be designed to be about 2.0D to 4.0D, e.g., 2.5D to 3.5D myopic. In some embodiments, the projected images will appear about 1.5 mm to about 2.5 mm in front of the peripheral retina, as they will be designed to be about 2.0D to 7.0D, preferably 2.5D to 5.5D myopic. In general, 1 mm in front of the retina corresponds to about 2.5D myopia, e.g., about 2.7D myopia.

[0094] This approach of peripheral stimulation of axial length change through choroidal thickening or thinning can be based on the repeatedly confirmed observation of the effectiveness of application of localized hyperopic or myopic defocus in stimulating axial length change of the eye 11. The length and duration of the peripheral stimulation can be based on available preclinical data in animal models, as known to those skilled in the art. For example, the rate of change of axial length can be obtained in repeated applications of the defocus stimulus, rather than a single sustained cycle of equivalent duration of imposed defocus.

[0095] In some embodiments, the duration and distribution of peripheral myopic defocus application depends on individual physiology and retinal shape. In some embodiments, the contact lens 10 includes a programmable processor, such as a microcontroller unit (MCU) or application specific integrated circuit (ASIC), for controlling the operation of the microdisplay 12. The contact lens 10 may include a real-time clock for regulating the treatment duration and periodicity by the treatment provider, which may be provided throughout the treatment. In some embodiments, the treatment provider tests whether nocturnal stimulation (sustained or repeated sequences of short pulses) has efficacy for an individual.

[0096] Glasses for retinal stimulation

[0097] 1A and 1B depict eyeglasses 70 suitable for the treatment of refractive errors of the eye and for incorporation according to the present disclosure. Although reference is made to eyeglasses, the light source can be provided on any visual device, such as an augmented reality ("AR") device described herein, to treat the refractive errors of the eye and reduce myopic deterioration or reverse myopia. A plurality of light sources are arranged to treat myopia. The plurality of light sources may comprise any suitable light source as described herein, such as, for example, a microdisplay or projection unit. In some embodiments, the light source is configured to provide illumination to the peripheral retina to promote changes in choroidal and scleral tissues corresponding to different changes in axial length, as described herein. The lens may comprise an optical zone with optical properties, e.g., refractive properties, configured to treat the refractive errors of the eye and reduce myopic deterioration or reverse myopia. This refractive treatment can be combined with retinal stimulation as described herein.

[0098] The glasses 70 may comprise one or more components of commercially available augmented reality glasses, such as the ORA-2 available from Optinvent (whose presence can be found on the internet at optinvent.com). The glasses 70 may comprise one or more displays 72 for retinal stimulation. The eyepiece displays 72 may be mounted on lenses 74. The lenses 74 may be spectacle lenses supported by a spectacle frame 76. The lenses 74 may be corrective or non-corrective lenses. The lenses 74 may be flat, spherically corrected, astigmatism corrected, or prism corrected. In some embodiments, the eyepiece displays are located away from the optical zone and provide clear central vision, such as the real world, over a field of view within a range of + / -2.0 degrees to + / -15.0 degrees or + / -2.0 degrees to + / -12.5 degrees. The optical axis may extend along the line of sight from the patient's gaze target, through the lenses 74, to the fovea of ​​the eye. In some embodiments, the glasses 70 comprise an eye tracker suitable for incorporation according to the present disclosure. The eyepiece display 72 can be programmed to selectively activate pixels 94 to provide peripheral retinal stimulation as described herein. In some embodiments, a layer of plastic substrate carrying microlenses is attached to the microdisplay to generate a desired level of defocus and stimulation at the retina. The selectively activatable pixels can be arranged to provide the appropriate eccentricity relative to the patient's line of sight to provide peripheral retinal stimulation as described herein.

[0099] In some embodiments, the eyepiece display 72 comprises a combination of a microdisplay and micro-optics. The microdisplay can be placed close enough to the eye that the eye does not accommodate and focus the light rays emanating from the eyepiece display, even within the full range of natural accommodation available to the human eye. In some embodiments, the micro-optics is configured to collect, substantially collimate, and focus the light rays emanating from the microdisplay. In some embodiments, the micro-optics is configured to form an image of the display in front of or behind the retina, as described herein. In some embodiments, the distance of the eyepiece display from the entrance pupil of the eye is within any suitable range, such as a range of about 10 mm to about 30 mm, or a range of about 18 mm to 25 mm, such as a distance of about 15 mm. The microdisplay can be placed on a transparent substrate, such as the front or back surface of the lens 74 of the eyeglasses 70. When the microdisplay is placed on the front surface of the lens 94, the focus of the microdisplay can be affected by a refractive correction on the back surface of the lens 94.

[0100] In some embodiments, the focus of a pixel in the microdisplay may vary based on its location on lens 74 and the refractive correction provided by the lens in that area. In some embodiments, the focus of a pixel may be fixed. In some embodiments, the focus of a pixel may vary based on the sensed position of the cornea, taking into account the refraction of the cornea and lens of the eye. In some embodiments, the pixel is defocused to create a defocused spot on the retina approximately 1 mm in diameter.

[0101] Light emitted by pixels 94 in the microdisplay of the eyepiece display can be substantially collimated or focused before being directed to the pupil of the eye. In some embodiments, the microlens array is aligned to the pixels of the eyepiece display such that light rays from the eyepiece display may enter the pupil and form an image in front of or behind the retina. In some embodiments, the width of the eyepiece display corresponds to the patient's field of view. In some embodiments, the extent of the eyepiece display may be substantially similar to the extent of the lenses 74 of the glasses 70. In some embodiments, the eyepiece display can be curved such that light rays from the pixels across the width of the display may be normal to the pupil plane. In some embodiments, a prism tilt is provided to the lenses in the microlens array to compensate for tilt of the plane of the microdisplay away from the pupil plane.

[0102] The writings related to this disclosure suggest that myopically defocused retinal stimulation is likely to be more effective in preventing myopia progression when applied from the periphery than when the foveal and / or macular images are also myopically defocused. The device can be configured to be worn for any suitable amount of time to provide myopia treatment. The myopia treatment device can be worn for an appropriate time for two years or longer treatment to maintain the wearer's emmetropia or to induce eye growth to emmetropia, for example, if the wearer has a tendency to shift to the myopic optical configuration of the eye. In some embodiments, the vision correction device is configured to be worn for a relatively long period of time, for example, for a period of one month and up to two years, for several hours per day, depending on, for example, the myopia reversal rate. The refractive prescription of the central optical zone can be changed in response to the treatment. For example, if myopia is reduced, the myopic correction of the central optics can be reduced. The refraction of the treated eye can be measured at any suitable time period, such as monthly, and the central optical zone prescription can be changed when appropriate.

[0103] In some embodiments, the device provides unimpaired central vision such that the wearer's quality of life and quality of vision are not adversely affected. In some embodiments, the central vision consists of a field of view of + / -12.5 degrees and covers the macula, while the foveal vision used for fixation has a field of view of + / -2.0 degrees. In some embodiments, the central vision consists of a field of view of + / -4.5 degrees and covers the macula, while the foveal vision used for fixation has a field of view of + / -2.0 degrees. In some embodiments, the defocused image is projected towards the periphery of the retina, for example, in the outer portion of the retina, within a range of eccentricity of 15 degrees to 40 degrees relative to the fovea, and can also be within a range of 20 degrees to 30 degrees. In some embodiments, the microdisplay 72 does not obstruct the central vision field. In some embodiments, the pixels 94 do not obstruct the central vision field.

[0104] As an alternative to, or in combination with, the decentration of a myopically defocused image, the device can be configured to illuminate an appropriately sized area of ​​the image or image footprint on the retinal image shell. Writings related to this disclosure suggest that it may be useful to illuminate at least a portion of each of the four quadrants of the retina. In some embodiments, each image on a retinal quadrant occupies an arc of about 45 degrees in the circumferential direction. In some embodiments, each image on a retinal quadrant occupies an arc of about 30 degrees in the circumferential direction. A suitable amount of illumination in the appropriate location can provide stimulation to the eye, reshaping the choroid and ultimately the sclera, reducing the axial length of the eye and leading to a reduction in myopia.

[0105] The microdisplay and optics can be configured in many ways to provide suitable stimulation at the outer regions of the retina toward the periphery. In some embodiments, the microdisplay and optics are configured to project light onto an outer region of the retina far enough from the fovea that the illumination remains substantially fixed even with eye movement. In some embodiments, the gaze point is monitored and the desired location of the pixel to be activated on the microdisplay is determined, for example by calculation with a processor, so that the image is projected onto the desired location on the retina, allowing sustained stimulation at the same retinal location. In some embodiments, the gaze point on the plane of the glasses or the microdisplay is calculated by monitoring the horizontal, vertical, and torsional displacements of the eye relative to a primary position.

[0106] The gaze point can be determined in many ways, for example, using an eye position sensor, such as a magnetic sensor or an optical sensor. In some embodiments, a search coil built into the eyeglass frame is used to track eye movement. The coil built into the eyeglass frame can be coupled to a magnetic structure placed on the eye, such as one or more of a coil on a contact lens, a coil embedded in the eye, a magnetic material on a contact lens, or a magnetic material embedded in the eye. In some embodiments, the sensor comprises an optical sensor, such as a position-sensing detector or an array sensor, to optically measure the position of the eye. The optical sensor can be configured to measure the position of the eye in many ways, for example, to measure the position of one or more of the corneal reflection from a light source, the pupil, the limbus, or the sclera. The eyeglass frame may support an additional light source to illuminate the eye, for example, to generate a corneal reflection. Data from the sensor can provide the location of the coaxial viewing corneal light reflection ("CSCLR") and thus the direction of the visual axis and the location of the fovea. Point of gaze, visual axis, optical axis, ocular node, and CSCLR are explained in “Ocular axes and angles: time for better understanding”, Srinivasan, S., in J CATARACT REFRACT SURG-VOL42,MARCH2016.

[0107] In some embodiments, the eyepiece display comprises a transparent flexible substrate that matches the curvature of the eyewear worn by the user. The eyepiece display can be mounted on the outside of the optical system and on the frame of the eyewear. The frame and temples can be made hollow or appropriately shaped to accommodate the electronics, including the electronic driver of the display, a rechargeable battery used to provide power to the system, and memory for storing algorithms that control the operation of the eyepiece display. The device can be recharged in many ways, for example, wirelessly by using a micro USB port or by using a recharging module.

[0108] In some embodiments, the processor using the eye position sensor may be configured to adjust optics, such as pixels in the microdisplay, in response to eye movement to reduce movement of the stimulated location of the retina. In some embodiments, a target location of the peripheral image is calculated from the location of the fovea based on information from the eye position sensor, and real-time ray tracing calculations provide the location of the pixel to be activated in the microdisplay. The time to selectively switch to the second plurality of pixels in response to eye movement may be less than 100 milliseconds, e.g., less than 20 milliseconds.

[0109] In some embodiments, the location of the pixel in the microdisplay that should be activated to form an outer image towards the periphery of the retina is referenced from the optical center of the eyeglass optics since that is the gaze point in the primary gaze. In some embodiments, the location of the gaze point is calculated by considering the eye movement relative to the position of the eye in the primary gaze and calculating the location of the pixel that should be activated with reference to the new gaze point. For example, FIG. 1A shows active pixel 94 when the patient is looking horizontally and straight ahead, so-called primary gaze, while FIG. 1B shows active pixel 94 when the patient is looking up and to the left. In such a case, the shape of the array of pixels may be the same, but translated to the top left, or the shape of the array may change. In some embodiments, the multiple light sources, e.g., active pixel 74, are configured to change to maintain alignment of the optical axis of the eye. This alignment can be provided according to eye movement and the optical axis of the eye using processor instructions configured to selectively activate the pixels.

[0110] In some embodiments, the eyepiece display module is mounted on the outside of the eyeglass lens. Alternatively, the eyepiece display can be mounted on the inside of the eyeglass lens. In some embodiments, the device is binocular and includes a microdisplay and an optical system for each eye of the wearer. The microdisplay can be optically coupled with one or more micro-optical components designed to substantially collimate the illumination generated and converged by the pixels of the microdisplay before it enters the pupil.

[0111] In some embodiments, the display 72, e.g., a display module, is mounted on the outside of the eyeglass lens and is matched with the eyeglass lens optics such that the eyepiece display can provide a field of view of + / -40 degrees or more, and the microdisplay can continue to provide peripheral retinal stimulation for the normal range of eye movements, typically + / -15 degrees laterally, such as + / -5 degrees laterally, + / -7 or + / -20 degrees vertically, and +10 to -20 degrees vertically, including downward gaze when reading or viewing nearby objects. In some embodiments, light from the microdisplay is transmitted through the eyeglass lens optics to provide the wearer's refractive correction.

[0112] In embodiments, the refractive correction comprises one or more of a spherical correction or a correction for astigmatism. In some embodiments, the correction comprises a prismatic correction for correction of strabismus and a correction for insufficient accommodation, which may vary across spectacle lens optics, such as cumulative sum lenses ("PALs"). In some embodiments, the micro-optics of the eyepiece display are configured to provide the myopic defocus required to generate peripheral retinal stimulation for prevention of myopia progression, as described herein, for example, with stimulation of outer regions of the retina with an image formed in front of the retina.

[0113] In some embodiments, the optical system is configured to form an image in front of the retina and comprises one or more of a single microlens (lenslet), multiple microlenses (lenslet array), compound lenses such as Gabor lenses, microprisms, or micromirrors, or combinations thereof. In some embodiments, the light baffles and micromirrors are arranged to ensure that the amount of light not captured by the micro-optics is substantially reduced, e.g., minimized, to reduce stray light and light escaping out the front side of the display.

[0114] In some embodiments, a pixel fill factor of less than 10% (0.1) is sufficiently sparse to provide a clear view of the foveal and macular images. In some embodiments, the fill factor is in the range of 0.01 to 0.3, and can also be in the range of 0.05 to 0.20. For example, an array of pixels with a pixel size of 5 microns and a pixel pitch of 20 microns leads to a fill factor of 0.06. A low fill factor may also reduce the complexity of the manufacturing process and reduce the cost of such micro-optical displays.

[0115] In some embodiments, the micro-optic array is designed to be optically aligned with the display such that light from a single or multiple pixels 94 can be collected, collimated, and focused and directed to the wearer's pupil in the primary line of sight. The density of these micro-optic elements can control the overall visibility of the eyepiece display. In some embodiments, the micro-optic has a low fill factor (preferably equal to or less than 0.1) so that the overall light transmission through the eyepiece display will be acceptable to the wearer and allow the patient to view objects.

[0116] In some embodiments, the device comprises a switchable micro-optic array that can be switched between a flat (no refractive power) state and an activated state by an electro-optic component, e.g., utilizing a liquid crystal or LC-based material that can be switched from one refractive index to another or from one polarization to another. In some embodiments, the micro-optic array does not scatter light or distort real-world images when not activated.

[0117] In some embodiments, the location of the pixel in the microdisplay that should be activated to form the outer image towards the periphery of the retina is referenced from the optical center of the eyeglass optics since that is the gaze point in the primary line of sight. In some embodiments, the location of the gaze point is calculated by taking into account the eye movement relative to the eye's position in the primary line of sight and calculating the location of the pixel that should be activated with reference to the new gaze point.

[0118] In some embodiments, multiple pixels are activated to form a light source that is imaged by the micro-optics. The optical design of the micro-optics and its separation from the microdisplay can be configured to accommodate the focal length of the image delivery system, the image magnification of the image projected onto the retina, and the blur caused by diffraction as measured as the Airy disk diameter of the optical delivery system.

[0119] According to some embodiments, technical specifications are given in Table 1.

[0120] [Table 1]

[0121] The optical resolution or quality of a peripherally projected image can be related to three factors: depth of focus, image magnification, and Airy disk diameter. The depth of focus of an eyepiece display depends on the focal length and aperture of the eyepiece display and the image magnification (Equation 1). Depth of focus=2N*c*(1+m)(Equation 1) When N is the f-number (f / D, where f is the focal length and D is the diameter), c is the circle of least confusion and m is the image magnification.

[0122] In a typical eye, 1.0D of myopic defocus shifts the image at best focus approximately 0.35mm forward.

[0123] Retinal resolution decreases with eccentricity such that retinal resolution within the desired range of eccentricity drops to 20 line pairs / mm at eccentricities within the range of 20-40 degrees. Even at these eccentricities, it has been found that the retina is capable of detecting the presence of stimuli at higher levels of spatial frequency. Thus, in some embodiments, a micro-optical array designed to form and project a peripheral image is capable of forming an image corrected for optical aberrations and for which the absolute value of the OTF is equal to or better than 0.3 at spatial frequencies of 50 lp / mm or greater.

[0124] The writings related to this disclosure suggest that the retina perceives changes in image blur caused by higher order aberrations (in addition to spherical defocus) present in the defocused image, including longitudinal chromatic aberration (LCA), higher order spherical aberration, astigmatism, etc., which are sensitive to the sign of the defocus. Based on the teachings provided herein, one skilled in the art can conduct experiments to determine whether the retina can perceive myopic and hyperopic blur when the depth of focus of the device exceeds or is approximately equal to the magnitude of the defocus. A device as described herein can be appropriately configured, for example, to provide the appropriate amount of defocus in the appropriate location.

[0125] The device can be configured to provide an appropriate image magnification ratio, diffraction that limits image resolution and depth of focus relative to the magnitude of myopic defocus being applied, and a rate of change of image blur or image sharpness gradient as a function of the magnitude of defocus. The human eye may have a lower threshold for blur perception. Since the strength of the growth signal to the retina and choroid depends on the magnitude of myopic defocus perceived in terms of image defocus, the range of defocus and blur perception can be taken into account when estimating the expected strength of the growth signal generated by a particular optical configuration for the magnitude of myopic defocus applied to the retinal image by the eyepiece display.

[0126] In some embodiments, the eyepiece display is configured to provide a clear, substantially undistorted view of the foveal and macular images for comfortable viewing. In some embodiments, the field of view of the central image is at least + / - 12 degrees or at least + / - 5 degrees, and may be larger to account for differences in interpupillary distance (IPD) of different wearers. The image quality and field of view of the real image can be provided with a substantially transparent eyepiece display and by reducing the fill factor of the emissive pixels in the microdisplay to be transparent. In some embodiments, a fill factor of less than 10% (0.1) is sufficiently sparse to provide a clear view of the foveal and macular images. In some embodiments, the fill factor is in the range of 0.01 to 0.3, and can also be in the range of 0.05 to 0.20. For example, an array of pixels with a pixel size of 5 microns and a pixel pitch of 20 microns would lead to a fill factor of 0.06. A low fill factor may also reduce the complexity of the manufacturing process and reduce the cost of such micro-optical displays.

[0127] In some embodiments, the micro-optic array is designed to be optically aligned with the display so that light from a single or multiple pixels can be collected, collimated, and focused and directed to the wearer's pupil in the primary line of sight. The population density of these micro-optic elements can control the overall visibility of the eyepiece display. In some embodiments, the micro-optics has a low fill factor (preferably equal to or less than 0.1) so that the overall light transmission through the eyepiece display will be acceptable to the wearer.

[0128] In some embodiments, the device comprises a switchable micro-optic array that can be switched between a flat (no refractive power) state and an activated state by an electro-optic component, e.g., utilizing a liquid crystal or LC-based material that can be switched from one refractive index to another or from one polarization to another. In some embodiments, the micro-optic array does not scatter light or distort real-world images when not activated.

[0129] Retinal stimulation source and circuitry

[0130] FIG. 2A shows an OLED microdisplay 12 mounted on the inner surface of a lens, such as a soft contact lens 10, optically coupled with a microlens array for projecting a defocused image onto the periphery of the wearer's retina.

[0131] FIG. 2B illustrates a lens, such as a soft contact lens 10, with multiple light sources and optical systems and associated circuitry, according to some embodiments.

[0132] Although Figures 2A and 2B refer to a contact lens, the lens may comprise one or more of a projector, an ophthalmic instrument, a TV screen, a computer screen, a handheld device such as a smartphone, a wearable device such as an eyeglass lens, an ocular display, a head mounted display, goggles, a contact lens, a corneal onlay, a corneal inlay, a keratoprosthesis, or an intraocular lens.

[0133] The contact lens 10 includes a plurality of projection units 18. Each of the plurality of projection units 18 includes a light source and one or more optics for focusing light in front of the retina, as described herein. Each of the optics may include one or more of a mirror, a plurality of mirrors, a lens, a plurality of lenses, a diffractive optic, a Fresnel lens, a light pipe, or a wave guide. The contact lens 10 may include a battery 20 and a sensor 22. The contact lens 10 may include a flexible printed circuit board (PCB) 24, and a processor may be mounted on the PCB 24. The processor may be mounted on the PCB 24 and coupled to the sensor 22 and the plurality of light sources 30. The soft contact lens 10 may also include wireless communication circuitry and an antenna to inductively charge the contact lens 10. Although reference is made to the battery 20, the contact lens 10 may include any suitable energy storage device. The soft contact lens 10 may include a lens body made of any suitable material, such as a hydrogel. The hydrogel can encapsulate the components of the soft contact lens 10 .

[0134] The processor can be configured with instructions to illuminate the retina using the multiple light sources 30. The processor can be programmed in many ways, for example, with instructions received using a wireless communication network. The processor can receive instructions for a user mobile device.

[0135] The sensor 22 can be coupled to the processor and can enable a user to control the contact lens 10. For example, the sensor 22 can be configured to respond to pressure, such as pressure from an eyelid. The processor can be coupled to the sensor 22 and can detect user commands.

[0136] The electronic control system may include a processor such as an ASIC or microcontroller, a rechargeable lithium ion solid state battery, a voltage ramp module such as a buck-boost converter, flash memory and EEPROM, an RFID module to provide wireless recharging, or an antenna, preferably positioned radially near the edge of the contact lens 10, as well as any combination thereof. The contact lens 10 may be comprised of a biocompatible material such as a soft hydrogel or silicone hydrogel material and may comprise any material composition that has been proven to be compatible with sustained wear on the eye 11 as the contact lens 10.

[0137] FIG. 2C illustrates the mechanical integration of the components of a lens, such as the contact lens 10 as in FIG. 2B. These components can be supported using a PCB 24. For example, a power source, such as a battery 20, can be mounted on the PCB 24 and coupled to the other components to provide a power function 21. A sensor 22 can be configured to provide an activation function 23. The sensor 22 can be mounted on the PCB 24 and coupled to a processor, which provides a control function 25 of the contact lens 10. The control function 25 may include a light intensity setting 27 and a light switch 29. The processor can be configured to detect, for example, a coded sequence of signals from the sensor 22, as well as a signal from the sensor 22 corresponding to an increase in intensity, a decrease in intensity, or an on / off signal from the sensor 22. The processor is coupled to the light projection unit 18, which can include a light source 30 and an optical system 32 to provide a projection function 31. For example, the processor can be coupled to a plurality of light sources 30 and control each of the light sources 30 in response to a user input to the sensor 22.

[0138] Optical configuration and projection optical system

[0139] In some embodiments, the optical arrangement 32 comprises a number of mirrors configured to collect the light emitted by the microdisplay 12 and then direct the light beam to the pupil of the eye 11 to form an eccentric retinal image as shown in Figures 3 and 4. The mirrors may collimate the light beam or direct the light beam towards the retina 33 with a suitable vergence movement to focus the light beam on the retina 33.

[0140] 3 and 4 refer to lenses such as contact lenses, similar optical configurations may also be used with one or more of the following lenses: projectors, ophthalmic equipment, TV screens, computer screens, handheld devices such as smartphones, wearable devices such as eyeglass lenses, ocular displays, head mounted displays, goggles, contact lenses, corneal onlays, corneal inlays, keratoprostheses, or intraocular lenses. Also, reference is made to myopic defocus, but defocus may comprise, for example, hyperopic defocus or an image focused on the retina.

[0141] Specifications of an exemplary optical configuration are shown in Table 2. [Table 2]

[0142] A comparison of the simulated image size and retinal resolution at 27 degrees eccentricity for the optical configuration shown in FIG. 3 indicates that the peripheral retina 33 at this eccentricity would be able to perceive this image.

[0143] In some embodiments, the three performance attributes of the optical configuration include one or more of the following:

[0144] 1. Image magnification ratio, which controls image resolution

[0145] 2. Depth of focus, which is controlled by the optical path length of the optical setup

[0146] 3. Diffraction, as measured by the Airy diameter

[0147] The mirror assembly shown in FIG. 3 achieves a depth of focus that is less than 1 D, allowing an applied defocus of 2.0-4.0 D or 2.0-7.0 D to be clearly perceived by the peripheral retina 33 at the specified eccentricities (20-30 degrees or 10-40 degrees).

[0148] In some embodiments, the spot size of an image focused in front of the retina 33 has a finer resolution than the resolution of the retina 33. The retinal resolution generally decreases as a function of eccentricity. For example, at an eccentricity angle of 0 degrees, the retinal resolution is about 10 micrometers. At an eccentricity of 5 degrees, the retinal resolution is about 30 micrometers. At an eccentricity of 20 degrees, the resolution is about 100 micrometers, and at 30 degrees, the retinal resolution is about 150 micrometers.

[0149] 5A and 5B show an analysis of the retinal image quality produced by the optical configuration of FIG. 3. Images formed by three of the four light sources 30 were simulated. The temple point is omitted because it is symmetrical with the nose point. The analysis shows that the image quality exceeds the resolving power of the retina 33 at 27 degrees of eccentricity. The modulation transfer function of the retinal image created by the mirror assembly of FIG. 3 shows that the aberrations of the optical elements, which are diffraction limited and deployed according to this embodiment, do not cause significant degradation of the image quality. Furthermore, the spatial resolution of the optical system exceeds the resolution of the retina 33 at the preferred image location.

[0150] Figure 6 shows an analysis of the depth of focus of the optical configuration shown in Figure 3. Every millimeter of distance from the retina 33 represents a defocus of 2.7D. The analysis shows that the depth of focus is small enough that a defocus of 0.5mm (1.35D) is perceptible by the retina 33 at the image entry point (27 degrees eccentricity). The depth of focus depends on the effective path length of the stimulation beam.

[0151] FIG. 7 shows a plot of the MTF values ​​versus defocus, illustrating the depth of focus of the images produced by each of the light sources (objects).

[0152] A second embodiment includes an optical system 32, comprising a converging or collimating lens, optically coupled to a light source 30, as shown in Figures 8A and 8B. In this configuration, a lens 34, which may comprise a single lens, is used to collimate the light output from the stimulus source and direct it through a lens, such as contact lens 10, to the cornea 37. Although reference is made to a contact lens, lens 10 may comprise one or more lenses of a projector, an ophthalmic instrument, a TV screen, a computer screen, a handheld device such as a smartphone, a wearable device such as a spectacle lens, an ocular display, a head mounted display, goggles, a contact lens, a corneal onlay, a corneal inlay, a keratoprosthesis, or an intraocular lens.

[0153] The effectiveness of the collimating lens 34 depends on its refractive index, which should be high enough to create a substantial difference in refractive index between the lens material and the material of the contact lens 10, which serves as the substrate. In this example, the refractive index of the built-in lens 34 is assumed to be 2.02 (e.g., the refractive index of lanthanum fluorosilicate glass LaSF5), but other materials may also be used.

[0154] The optical performance of the embodiment of Figures 8A and 8B is shown in Figures 9 and 10. Images formed by three of the four light sources 30 were simulated. The temple points are omitted since they are symmetrical with the nose points. Every millimeter of distance from the retina 33 represents a defocus of 2.7D. The present analysis shows that the depth of focus is substantially higher than 1D such that the image blur caused by a defocus of 0.5mm (1.35D) may be imperceptible by the retina 33 at the image entry point (27 degrees eccentricity).

[0155] The analysis shows that the image quality exceeds the resolving power of the retina 33 at 27 degrees of eccentricity. The optical path length of the single lens design is much shorter in this case, and therefore the image magnification is substantially higher (110x, as opposed to 8x or 20x for the reflective design). The spatial frequency resolution (absolute value of OTF) at 50% contrast is about 15 line pairs per millimeter ("lp / mm"), which is lower compared to 50 lp / mm for the reflective design. The depth of focus was estimated for this embodiment, again using the Liou Brennan eye model, to simulate the ocular optical system, including ocular aberrations, as shown in FIG. 10. The depth of focus is greater than 1.0D, indicating that the change in image resolution as a function of defocus may not be easily perceptible by the peripheral retina 33, as described herein, especially since the resolution capabilities of the retina 33 at its eccentricities (20-30 degrees or 10-30 degrees), derived mainly from the rods, are relatively poor.

[0156] A third embodiment includes a light pipe 36 to increase the optical path length, as shown in Figures 11A and 11B. The light pipe 36 provides an increased optical path length, which can reduce image magnification and retinal image size. However, the depth of focus is relatively large and the resolution is relatively coarse (15 lp / mm at 50% MTF).

[0157] Reference is made to a light pipe 36 on the cornea 37 as would occur with a contact lens, however the lens combined with the light pipe 36 may comprise one or more of a projector, ophthalmic equipment, a TV screen, a computer screen, a handheld device such as a smart phone, a wearable device such as an eyeglass lens, an ocular display, a head mounted display, goggles, a contact lens, a corneal onlay, a corneal inlay, a keratoprosthesis, or an intraocular lens.

[0158] Many other optical configurations may be used, including the use of a microlens array with a point source, the use of diffractive optics to use thinner lenses, the generation of multiple retinal images using a single point source and optical processing unit, etc. In all cases, the three characteristics listed above may be used as metrics to evaluate the suitability of a particular design.

[0159] Each embodiment disclosed herein can be combined with any one or more of the other embodiments disclosed herein, and one of ordinary skill in the art will recognize many such combinations as being within the scope of the present disclosure.

[0160] Exemplary Lens Embodiments

[0161] The methods and apparatus of the present disclosure are well suited for combination with many types of lenses, such as one or more of smart contact lenses, contact lenses with antennas and sensors, contact lenses with integrated pulse oximeters, contact lenses with phase map displays, electro-optical contact lenses, contact lenses with flexible conductors, autonomous eye tracking contact lenses, electrochromic contact lenses, dynamic diffractive liquid crystal lenses, auto-accommodation lenses, image display lenses with programmable phase maps, lenses with tear activated microbatteries, tear film sensing contact lenses, lenses with multi-color LED arrays, contact lenses with capacitive sensing, lenses for detecting overlap of ophthalmic devices with the eyelids, lenses with active accommodation, lenses with electrochemical sensors, lenses with enzymes and sensors, lenses including dynamic visual field modulation, lenses for measuring pyruvate, lenses for measuring urea, lenses for measuring glucose, lenses with tear conductivity sensors, lenses with ocular displays with phase maps, or lenses with electrochemical sensor chips.

[0162] A lens, such as a soft contact lens 10, is shown in Figure 12. Although reference is made to a contact lens, the lens 10 may comprise one or more of a projector, an ophthalmic instrument, a TV screen, a computer screen, a handheld device such as a smart phone, a wearable device such as an eyeglass lens, an ocular display, a head mounted display, goggles, a contact lens, a corneal onlay, a corneal inlay, a keratoprosthesis, or an intraocular lens.

[0163] The present contact lens 10 comprises a base or carrier contact lens with built-in electronics and optics. The base soft contact lens 10 is made of a biocompatible material, such as hydrogel or silicone hydrogel polymer, designed to be comfortable for sustained wear. In some embodiments, the contact lens 10 has a central optical zone 14 with a diameter in the range of 6 mm to 9 mm, e.g., in the range of 7.0 mm to 8.0 mm. The central optical zone 14 is surrounded by an outer annular zone, such as a peripheral zone 16 with a width in the range of 2.5 mm to 3.0 mm. The outer annular zone is surrounded by an outermost edge zone 18 with a width in the range of 0.5 mm to 1.0 mm. The optical zone 14 is configured to provide refractive correction and can be, for example, spherical, toric, or multifocal in design. The outer annular zone around the optical zone 14 is configured to conform to the corneal curvature and may include a rotational stabilization zone for translational and rotational stability while allowing movement of the contact lens 10 on the eye 11 with eye blinking. The edge zone 18 may have a thickness in the range of 0.05 mm to 0.15 mm and may terminate in a wedge shape. The overall diameter of the soft contact lens 10 may be in the range of 12.5 mm to 15.0 mm, for example in the range of 13.5 mm to 14.8 mm.

[0164] The integrated light source 30 and electronics are preferably located in the outer annular zone of the contact lens 10, as shown in Figure 12. The central optical zone 14, according to some embodiments, is preferably free of electronics and light source 30 so as not to impair the quality of central foveal or macular vision. In some embodiments, the limbal zone 18 is free of circuitry to maintain contact with the corneal surface and provide comfort.

[0165] The light sources can be arranged on the contact lens in many ways. For example, the light sources can be arranged in a substantially continuous ring around the central optical zone. In some embodiments, multiple light sources and multiple optics (e.g., lenses, mirrors, or light guides) are combined together to form a continuous ring of illumination.

[0166] The contact lens 10 of FIG. 12 comprises a body made of a soft biocompatible polymer with high oxygen permeability, built in with a transparent film in which all electronic and optical components are incorporated. The transparent film may comprise a transparent printed circuit board ("PCB") substrate. The PCB thickness may be in the range of about 5 microns to about 50 microns, and may comprise multiple film layers to utilize both sides of the PCB substrate for incorporation of electronics. The PCB substrate may be curved to conform to the geometry of the base contact lens 10, for example, with a curvature in the range of about 7.5 mm to about 10.0 mm, for example, in the range of about 8.0 mm to about 9.5 mm. The PCB substrate may be configured for suitable oxygen permeability. In some embodiments, the PCB is perforated to improve the permeability of oxygen, tears, nutrients, and carbon dioxide therethrough. In some embodiments, the PCB has a low tensile modulus, for example, in the range of about 1 MPa to about 50 MPa, although stiffer films, for example, may also be used. In some embodiments, preferred materials for transparent flexible PCB substrates include polyimide, which is cast from liquid or solution, spin cast onto a flat substrate, and subsequently thermally cured, such as Kapton. TMThe polyimide may be in the form of a polyamic acid, such as polyimide 1, 1-diaminophenyl ether, polyamide 1, or polyamide 2.

[0167] The contact lens 10 may include one or more components shown in FIG. 12. The electronic system architecture shown in FIG. 12 includes a plurality of light sources 30 mounted on a bus, a microcontroller 38 including a power and data management system, an on-board memory, and an RFID module, a sensor designed to detect a physical or physiological trigger and issue a signal to turn the light source 30 on or off, an antenna 41 for wireless exchange of data, also functioning as a wireless receiver of power, operating on a single or multiple frequency bands for data and power transmission, and a rechargeable solid-state lithium-ion battery 20. In some embodiments, the microcontroller 38 includes an application specific integrated circuit ("ASIC"). The plurality of light sources 30 may include a micro light source 30 as described herein.

[0168] The light sources 30 may be positioned along a circumference with a diameter within the range of 1.5 mm to 5.0 mm from the center.

[0169] 13 shows a ray tracing analysis of an image of the light source 30 formed on an outer region of the retina 33, such as the peripheral retina 33. In this simulation, the anterior chamber depth is assumed to be 4.1 mm, typically 2.9 mm to 5.0 mm, for a human subject, the axial length is assumed to be 25.0 mm, and the contact lens 10 is positioned on the cornea. The miniature light source 30 is placed 1.9 mm away from the center of the contact lens 10, leaving a clear, 3.8 mm diameter central optical zone 14.

[0170] 12 and 13, a combination of a light source 30 and a lens, such as a microlens, can be used to direct light to an outer region of the retina 33. The microlens can be configured to collect the light emitted by the light source 30. The collected light can be one or more of collimated and focused and directed to the pupil of the eye 11. In some embodiments, the projection system comprises a combination of a micro-light source 30 and image forming optics 32.

[0171] The light source 30 may comprise one or more of an organic light emitting diode (OLED), a quantum dot light emitting diode (QLED), a transparent light emitting diode (TOLED), an inorganic light emitting diode (i-LED), a CRT display, or a vertical cavity surface emitting laser (VCSEL). The light source 30 may comprise one or more pixels incorporated on a transparent or opaque substrate. The light source 30 may comprise one or more display components, such as, for example, a passive matrix or an active matrix. In some embodiments, the size of the individual pixels is in the range of 1 to 10 microns, for example, in the range of 2 to 5 microns. The brightness of each of the plurality of pixels when turned on may be greater than 500 nits (Cd / m 2 ), greater than 5000 nits, or in the range of 10,000 to 25,000 nits.

[0172] The resolving power of the retina 33 is highest in the center, or fovea. A healthy young person has an angular resolution of 0.6 arc minutes, which is comparable to 20 / 12 in Snellen acuity. The resolving power is typically reduced to 20 / 200 (10 arc minutes) at 25 degrees of eccentricity. At this eccentricity, there are few, if any, cones present, and the distribution density of rods is also greatly reduced.

[0173] In some embodiments, the image delivery system provides an image resolution that is equal to or exceeds the level of retinal image resolution. In some embodiments, if the projected image resolution exceeds the resolution capabilities of the retina 33 at the location of the image, no additional benefit may be expected. In some embodiments, the image spot size at the retinal periphery is therefore 150 microns or less.

[0174] The wavelength of light emitted by the light source 30 can be configured in many ways. The wavelength of light emitted by the light source 30 can be determined by clinical studies according to the present disclosure. In some embodiments, the wavelength of the light source 30 comprises light that corresponds to, e.g., substantially matches, the peak sensitivity of the retinal photoreceptors at the desired eccentricity. In some embodiments, the light is projected at an eccentricity of 10-30 degrees, such as 20-30 degrees, where rods are dominant, and the light from the source comprises a wavelength within a range of about 410 nm to 600 nm, such as about 490 nm to 530 nm, e.g., about 500-520 nm, e.g., about 502-512 nm. In some of the wavelength simulations disclosed herein, 507 nm light is used as the input wavelength parameter. The optical designs disclosed herein are applicable to all wavelengths, even though the precise results of the optimized design parameters may vary with wavelength due to chromatic dispersion of the materials that make up the projection unit.

[0175] Writings related to this disclosure suggest that two design constraints may influence the selection of design input parameters in some of the embodiments that follow. These are:

[0176] 1. The dimensions of the projection unit 18 such that it can be integrated into the contact lens 10 without increasing the lens thickness too much. In some embodiments, the maximum lens thickness in the outer annular zone is 400 microns, which is consistent with current soft contact lenses for refractive correction.

[0177] 2. The optical path length between the micro light source 30 and the image forming system. This relates to controlling the image magnification and the amount of image blur caused by diffraction, which can be quantified as the Airy disk diameter. The image magnification is given by the ratio of the focal length of the image projection unit to the focal length of the eye 11, which is generally assumed to be 17 mm for a first order estimate. In some embodiments, this is specific to an individual eye. In some embodiments, the Airy disk diameter (2.44 x λ (in microns) x f-number) is equal to or less than the retinal resolution limit at the image location. For example, the minimum spot size at 25 degrees eccentricity is 150 microns, so the Airy disk diameter should not exceed 150 microns and can be less than 150 microns. Since the focal length of the eye 11 is fixed, the aperture of the projection optics controls the Airy disk diameter at any wavelength.

[0178] In some embodiments, the size of the Airy disk of collection optics and light source 30 and associated image as described herein is related to retinal image resolution. For example, at 30 degrees, 25 degrees, 20 degrees, 15 degrees, and 10 degrees, the Airy disk size may be about 150 micrometers ("microns", "μm") about 125 μm, about 100 μm, about 75 μm, and about 60 μm or less, respectively.

[0179] The imaging system can be configured in many ways, including, but not limited to, diffractive optical elements, Fresnel lenses, refractive optics, or reflective optics.

[0180] The following simulations provide optical results according to some embodiments disclosed herein. [Table 3]

[0181] In some embodiments, the area covered by the overall image is preferably 5-10 degrees by 30-45 degrees, or 150-450 degrees per light source. 2, or approximately 3.0 to 6.0 mm 2 100μm。 In some embodiments, four such light sources 30 in each quadrant of the contact lens 10 deliver four such peripheral images for optimal neural stimulation to the retina 33. A second simulated embodiment of the image delivery system is shown in FIG. 3. In this embodiment, a system of convex 26 and concave 28 micromirrors is used to increase the optical path length and thereby the image magnification of the peripheral retinal images. FIG. 4 shows the optical path of the peripheral images through the eye 11 for this embodiment. An exemplary light source 30 can be defined assuming that the diameter of the light source 30 is 10 μm and the thickness is 100 μm. Four object points 40 can be defined to simulate image quality as shown in FIG. 14. With reference to FIG. 14, the simulated light source 30 is shown with a dashed circle of 10 μm, and the simulated object points 40 include the smaller circle and the center point of each of the smaller circles. Table 3 shows the input parameters of the simulation.

[0182] The outputs of the simulation are image magnification and size, image quality, and depth of focus. The same input and output parameters were used to simulate all preferred embodiments. The image size of the first preferred embodiment was found to be 200 microns, and the image magnification was 20x. The image quality simulation results are shown in Figure 15 for this simulation. All MTF plots are virtually identical. The MTF plots show that the peripheral image resolution is substantially better than the retinal resolution limit at this eccentricity.

[0183] The depth of focus of the peripheral image is also simulated for the reflective optics in a second simulation and is shown in FIG. 16. In some embodiments, the image is optimally formed at a distance of 2.0 mm in front of the retina 33 and is myopically defocused on the retina 33. In some embodiments, this myopic defocus induced blur overcomes the effect of the depth of focus such that the retina 33 perceives a blurred image as it perceives neural stimulation, moves forward, and reduces the axial length of the eye 11. In some embodiments, the neural stimulation is sufficient to reduce the axial growth of the eye 11.

[0184] FIG. 17 shows the effect of image blur caused by myopic defocus in the form of loss of contrast, i.e., absolute value of the simulated MTF plot shown for a particular spatial frequency (20 / 200 or 10 arc minutes) for the second simulation. The increase in spot size shown in FIG. 16 is reflected and coincides with the loss in magnitude of the MTF plot as a function of the magnitude of the myopic defocus. The second simulation shows that the focal length of the projection unit is 0.85 mm with an image size of 200 microns and the image magnification is 20 times. The Airy disk diameter is calculated to be 8.9 microns, while the Raleigh criterion is 10.9 microns.

[0185] Reference is again made to Figures 8A and 8B, which respectively show a lens for collecting light from the light source 30 and directing the light towards the retina 33, and the path of the light along the eye 11. In some embodiments, the light source 30 faces a refractive lens that approximately collimates the light, which is finally projected in front of the peripheral retina 33, creating a myopic defocus of the peripheral image. Reference is made to a refractive lens, but other lenses such as diffractive optics and gradient index (GRIN) lenses can also be used. Table 4 shows the design parameters of the refractive lens used for the third simulation of the peripheral image. [Table 4-1] [Table 4-2]

[0186] The results of these simulations show that the image size is 1,100 microns with an image magnification of 110. MTF plots are shown in FIG. 18 for the four object points 40 shown in FIG. 14. The magnitude of the MTF plots at high spatial frequencies is substantially lower than for the reflective optics. The MTF plots show that the image resolution is adequate for an image with an eccentricity of 27 degrees. The optical design of the second preferred embodiment leads to a much larger depth of focus, as shown in FIG. 19. This means that in some embodiments, the effective image blur is much less for myopic defocus in the range of 2D to 5D compared to the reflective optics according to the first and second simulations. The increased depth of focus is reflected in the MTF plots shown in FIG. 20, which may have less dependence on the magnitude of myopic defocus compared to the reflective optical configurations shown in FIGS. 3 and 4.

[0187] The third optical simulation shows that the refractive optical system can successfully project the peripheral retinal image with acceptable image size and image magnification and depth of focus, although the image size, magnification, and depth of focus may be somewhat larger than the reflective configuration of the second simulation.

[0188] Although the MTF values ​​at high spatial frequencies (50 lp / mm and above) are lower for the refractive optics design than the reflective design, the image quality at high spatial frequencies may be somewhat less relevant at the peripheral locations of the retinal image due to reduced visual acuity. A third simulation shows that the focal length of the projection unit is 0.15 mm with an image size of 1,100 microns and the image magnification is 110x. The Airy disk diameter was calculated to be 36.7 microns, while the Raleigh criterion is 44.8 microns.

[0189] 11A and 11B, which again show a light guide, a fourth simulation was performed for this configuration, which includes a light guide, a mirror, and a lens. In the simulated embodiment, a focusing lens is located at the end (exit aperture) of the light pipe. In some embodiments, the light pipe includes a curved lens surface on the end to focus the light. In this light guide embodiment, the projection optics includes a light guide, which includes a mirror and a lens.

[0190] In some embodiments, the light source 30 is placed near an outer portion of the contact lens 10, e.g., the periphery, and light from the source is guided to a mirror that collects the light and deflects it toward the eye 11 to produce an image with myopic defocus as described herein in front of the peripheral retina 33. In some embodiments, the function of the light guide is to increase the length of the light path so as to reduce image magnification and increase the resolution of the image formed in front of the retina 33. [Table 5]

[0191] Table 5 gives the properties of the projection system used in the fourth simulation of the peripheral retinal image quality produced by the inner light guide embodiment. The image magnification was 14 with an image size of 140 microns. These simulations reveal that the image magnification is acceptable and the depth of focus is greater than reflective optics, although not as great as refractive optics. The fourth simulation shows that the focal length of the projection unit is 1.21 mm with an image size of 140 microns and a magnification of 14 times. The Airy disk diameter was calculated to be 34.8 microns, while the Raleigh criterion is 42.6 microns.

[0192] The three results of the second, third and fourth simulations for the three corresponding configurations were compared with each other in terms of their size, the depth of focus produced by defining the sharpness gradient of the defocused image as a function of the magnitude of myopic defocus, respectively, and the beam diameter. The results show that the second simulation with reflective optics has the best sharpness gradient, while the embodiment with refractive optics has the smallest sharpness gradient, and the light guide based projection unit provides a limited sharpness gradient, as shown in FIG. 24. Each of these approaches can be configured to reduce axial length growth according to the teachings disclosed herein.

[0193] The three embodiments also differ significantly in terms of optics diameter, as shown in Table 6. [Table 6]

[0194] The reflective optics and light source 30 can be configured in many ways, and additional simulations can be performed to determine the appropriate configuration according to the teachings disclosed herein. For example, the clarity at the central object point shown in FIG. 14 can be ignored since its contribution to neural stimulation is likely to be limited. Such simulations and optimizations can allow for a reduction in the diameter of the projection unit and its thickness, which can be useful when the system is integrated into a contact lens 10, which provides a high level of comfort to the wearer, as described herein. The design input parameters for the fifth simulation are shown in Table 7.

[0195] [Table 7-1] [Table 7-2]

[0196] The results show that the image magnification can be increased to 25 to provide an image size of 250 microns for a 10 micron source, which is acceptable for peripheral images in front of the retina 33, according to embodiments disclosed herein. The output of these fourth image simulations is shown in Figures 25 and 26. The sharpness gradient, which is the variation of the MTF at a single spatial frequency as a function of the image spot size or magnitude of myopic defocus, is still very acceptable, while providing for the reduced size of the projection system.

[0197] As detailed herein, the computing devices and systems described and / or illustrated herein broadly represent any type or form of computing device or system capable of executing computer-readable instructions such as those contained within the modules described herein. In their most basic configurations, these computing devices may each include at least one memory device and at least one physical processor.

[0198] The term "memory" or "memory device," as used herein, generally refers to any type or form of volatile or non-volatile storage device or medium capable of storing data and / or computer-readable instructions. In one embodiment, a memory device may store, load, and / or maintain one or more of the modules described herein. Examples of memory devices include, but are not limited to, random access memory (RAM), read-only memory (ROM), flash memory, hard disk drive (HDD), solid-state drive (SSD), optical disk drive, cache, any variation or combination of one or more thereof, or any other suitable storage memory.

[0199] Additionally, the term "processor" or "physical processor," as used herein, generally refers to any type or form of hardware-implemented processing unit capable of interpreting and / or executing computer-readable instructions. In one embodiment, a physical processor may access and / or modify one or more modules stored in a memory device as described above. Examples of physical processors include, but are not limited to, a microprocessor, a microcontroller, a central processing unit (CPU), a field programmable gate array (FPGA) implementing a soft-core processor, an application specific integrated circuit (ASIC), one or more portions thereof, one or more variations or combinations thereof, or any other suitable physical processor.

[0200] Although illustrated as separate elements, the method steps described and / or illustrated herein may represent portions of a single application. Additionally, in some embodiments, one or more of these steps may represent or correspond to one or more software applications or programs that, when executed by a computing device, may cause the computing device to perform one or more tasks, such as method steps.

[0201] In addition, one or more of the devices described herein may convert data, a physical device, and / or a representation of a physical device from one form to another. For example, one or more of the devices listed herein may receive image data of a sample to be converted, convert the image data, output a result of the conversion, determine a 3D process, use the result of the conversion to perform the 3D process, store the result of the conversion, and produce an output image of the sample. Additionally or alternatively, one or more of the modules listed herein may execute on a computing device, store data on the computing device, and / or otherwise interact with the computing device to convert a processor, a volatile memory, a non-volatile memory, and / or any other portion of a physical computing device from one form of computing device to another form of computing device.

[0202] The term "computer-readable medium" as used herein generally refers to any form of device, carrier, or medium capable of storing or carrying computer-readable instructions. Examples of computer-readable media include, but are not limited to, transmission-type media, such as carrier waves, and non-transitory type media, such as magnetic storage media (e.g., hard disk drives, tape drives, and floppy disks), optical storage media (e.g., compact discs (CDs), digital video discs (DVDs), and BLU-RAY® discs), electronic storage media (e.g., solid-state drives and flash media), and other distribution systems.

[0203] Those skilled in the art will recognize that any process or method disclosed herein can be modified in many ways. The process parameters and sequences of steps described and / or illustrated herein are given by way of example only and can be varied as desired. For example, although the steps illustrated and / or described herein may be illustrated or discussed in a particular order, these steps do not necessarily have to be performed in the order illustrated or discussed.

[0204] The various exemplary methods described and / or illustrated herein may also omit one or more of the steps described or illustrated herein, or may comprise additional steps in addition to those disclosed. Furthermore, the steps of any method as disclosed herein can be combined with any one or more steps of any other method as disclosed herein.

[0205] Unless otherwise noted, the terms "connected to" and "coupled to" (and derivatives thereof), as used in the specification and claims, should be interpreted as allowing for both direct and indirect (i.e., via other elements or components) connections. In addition, the terms "a" or "an" should be interpreted as meaning "at least one of." Finally, for convenience, the terms "including" and "having" (and derivatives thereof), as used in the specification and claims, are intended to be interchangeable and have the same meaning as the word "comprising,".

[0206] A processor as disclosed herein may be configured with instructions to perform any one or more steps of any method as disclosed herein.

[0207] The terms "first," "second," "third," etc. may be used herein to describe various layers, elements, components, regions, or sections without reference to any particular order or sequence of events, but it should be understood that these terms are merely used to distinguish one layer, element, component, region, or section from another layer, element, component, region, or section. A first layer, element, component, region, or section as described herein could also be referred to as a second layer, element, component, region, or section without departing from the teachings of the present disclosure.

[0208] As used herein, the term "or" is used inclusively to refer to items as alternatives and in combination.

[0209] Each embodiment disclosed herein can be combined with any one or more of the other embodiments disclosed herein, and one of ordinary skill in the art will recognize many such combinations as being within the scope of the present disclosure.

[0210] This disclosure includes the following notes:

[0211] Addendum 1. A device for providing stimulation to the retina of an eye, the device comprising one or more optical systems for projecting one or more images onto the retina outside the fovea to encourage one or more of changes in axial length or choroidal thickness of the eye.

[0212] Clause 2. The device of Clause 1, wherein the one or more images comprise one or more of a still image or a dynamic image.

[0213] Clause 3. The device of clause 2, wherein the image comprises a dynamic image with a refresh rate in the range of 1 Hz to 200 Hz.

[0214] Clause 4. The device of clause 1, wherein the one or more images comprise one or more of monochromatic or polychromatic light having wavelengths in the range of 400 nm to 800 nm.

[0215] Clause 5. The device of clause 1, wherein the image has information or content in a spatial frequency range of 1 cycle / degree to 60 cycles / degree, optionally 1 cycle / degree to 10 cycles / degree.

[0216] Addendum 6. The device of Addendum 1, wherein the image has a contrast within the range of 99.9% to 2.5%.

[0217] Clause 7. The device of clause 1, wherein the image has an eccentricity relative to the fovea in the range of 5 degrees to 40 degrees.

[0218] Clause 8. The device of clause 7, wherein the image illuminates the retina within the area with a pattern that extends substantially continuously 360 degrees around the fovea.

[0219] Clause 9. The device of clause 7, wherein the image illuminates a portion of the retina within a range.

[0220] Clause 10. The device of Clause 1, further comprising circuitry for stimulating the retina with one or more images using transient illumination comprising one or more of continuous illumination, intermittent illumination, periodic illumination, or aperiodic illumination.

[0221] Clause 11. The device of clause 10, wherein the temporary illumination comprises periodic illumination for a duration in the range of 1 second to 24 hours.

[0222] Clause 12. The device of clause 10, wherein the temporary illumination comprises intermittent illumination for a duration in the range of 1 second to 24 hours.

[0223] Clause 13. The device of Clause 10, wherein the circuitry is configured to illuminate the retina when the subject is awake, asleep, or one or more of asleep or awake.

[0224] Clause 14. The device of Clause 1, further comprising circuitry for stimulating the retina with one or more images using a spatial illumination pattern comprising one or more of a continuous spatial illumination pattern, an intermittent spatial illumination pattern, a periodic spatial illumination pattern, or a non-periodic spatial illumination pattern.

[0225] Addendum 15. The device of Addendum 1, wherein the one or more images have a brightness in the range of 1 to 1000 Tronds.

[0226] Addendum 16. The device of Addendum 1, wherein the one or more optical systems are configured to project the one or more images with a brightness in the range of 100 to 50,000 nits or in the range of 1 to 10,000 nits.

[0227] Addendum 17. The device of Addendum 1, wherein the one or more images are corrected for refractive error of the eye.

[0228] Addendum 18. The device of Addendum 1, wherein the one or more images are defocused to one or more locations on the retina where the one or more images illuminate the retina.

[0229] Clause 19. The device of clause 18, wherein the one or more images are myopically defocused within a range of 2.0D to 7.0D, optionally 2.0D to 5.0D.

[0230] Clause 20. The device of clause 18, wherein the one or more images are hyperopically defocused by an amount in the range of 2.0D to 7.0D, optionally 2.0D to 5.0D.

[0231] Addendum 21. The device of Addendum 1, wherein the one or more optical systems comprise components of an optical projection system.

[0232] Addendum 22. The device of Addendum 21, wherein the light projection system comprises one or more components of a projector, an ophthalmic device, a TV screen, a computer screen, a handheld, a mobile computing device, a tablet computing device, a smartphone, a wearable device, an eyeglass lens, an ocular display, a head mounted display, goggles, a contact lens, an implantable device, a corneal onlay, a corneal inlay, a keratoprosthesis, or an intraocular lens.

[0233] Addendum 23. The device of Addendum 21, further comprising a support coupled to the projection system, the support comprising one or more of an ophthalmic device, a TV screen, a computer screen, a handheld, a mobile computing device, a tablet computing device, a smartphone, a wearable device, an eyeglass lens frame, an eyeglass lens, an eyepiece display, a head mounted display, goggles, a contact lens, an implantable device, a corneal onlay, a corneal inlay, a keratoprosthesis, or an intraocular lens.

[0234] Addendum 24. The device of Addendum 1, comprising a plurality of light sources, and one or more optical systems coupled to the plurality of light sources and comprising a plurality of projection optical systems for projecting a plurality of images in front of the retina.

[0235] Addendum 25. The device of Addendum 24, wherein the multiple projection optical systems are arranged to project multiple images of the multiple light sources onto multiple outer regions of the retina of the eye with an eccentricity in the range of 5 degrees to 30 degrees relative to the fovea of ​​the eye, optionally in the range of 15 degrees to 30 degrees.

[0236] Addendum 26. The device of Addendum 24, wherein each of the plurality of projection optical systems is arranged to project an image that is myopically defocused onto the retinal surface, the amount of defocus being in the range of 2.0D to 7.0D, optionally in the range of 2.0D to 5.0D.

[0237] Addendum 27. The device of Addendum 24, wherein each of the plurality of projection optical systems is located 1.5 mm to 5.0 mm from the center of the contact lens, and optionally, the plurality of projection optical systems are located along a circular circumference.

[0238] Addendum 28. The device of Addendum 24, wherein the multiple projection optical systems include multiple image-forming optical systems optically coupled to the multiple light sources and projecting multiple images in front of the surface of the retina.

[0239] Addendum 29. The device of Addendum 28, wherein each of the plurality of light sources has a maximum transverse distance not exceeding 26 microns, optionally no greater than 10 microns, optionally comprising a diameter.

[0240] Addendum 30. The device of Addendum 28, wherein each of the multiple projection optical systems comprises one or more of a mirror, a lens, or a light guide.

[0241] Addendum 31. The device of Addendum 30, wherein each of the plurality of image-forming optics comprises one or more of a diffractive element, a Fresnel lens, or a compound Gabor lens.

[0242] Addendum 32. The device of Addendum 30, wherein each of the plurality of image-forming optical systems has a maximum traversal distance in the range of 200 microns to 1.5 mm, optionally comprising a diameter.

[0243] Clause 33. The device of clause 30, wherein each of the plurality of image-forming optics is aspheric and corrected for image aberrations.

[0244] Clause 34. The device of clause 30, wherein each of the plurality of image-forming optics comprises a combination of convex and concave mirrors.

[0245] Addendum 35. The device of Addendum 33, wherein each of the plurality of image forming optical systems forms an image in front of an outer portion of the retina at an eccentricity within a range of 1 degree to 30 degrees from the fovea, optionally 10 degrees to 30 degrees from the fovea, optionally 15 degrees to 30 degrees, and further optionally 25 degrees to 30 degrees.

[0246] Addendum 36. The device of Addendum 33, wherein each of the plurality of image-forming optical systems creates an image in front of the retina using an image with a magnification ratio in the range of 5 to 20 or in the range of 25 to 100.

[0247] Clause 37. The device of clause 24, wherein the image of the anterior portion of the outer portion of the retina has a modulation transfer function magnitude of 0.75 or greater at a spatial frequency of 10 lp / mm, 0.40 or greater at a spatial frequency of 30 lp / mm, optionally 0.75 or greater at a spatial frequency of 10 lp / mm, or 0.40 or greater at a spatial frequency of 50 lp / mm.

[0248] Addendum 38. The device of Addendum 30, wherein each of the multiple projection optical systems comprises an image forming optical system including a collimating optical system configured to form an image in front of the retina.

[0249] Clause 39. The device of clause 30, wherein the projection optics comprises a single lens for functioning as both the collimating optics and the image-forming optics.

[0250] Clause 40. The device of clause 30, wherein the projection optics comprises image forming optics for creating an image in front of the outer portion of the retina with an eccentricity of 30 degrees or less and a depth of focus of 1.0D or less.

[0251] Addendum 41. The device of Addendum 39, wherein the optical system creates an image in front of an outer portion of the retina with an eccentricity of 30 degrees or less, and the modulation transfer function of the image decreases by a minimum of 0.1 units for 1.0 D of defocus, optionally, the 1.0 D of defocus constituting an incremental defocus.

[0252] Clause 42. The device of clause 24, wherein the multiple light sources comprise multiple microdisplays.

[0253] Clause 43. The device of clause 24, wherein the multiple light sources comprise multiple light emitting diodes (LEDs).

[0254] Addendum 44. The device of Addendum 24, wherein each of the plurality of optical elements comprises a mirror assembly that collimates light emitted by a corresponding microdisplay and directs the resulting light beam into the pupil of the eye, where the light beam is focused to form a peripheral image in front of the retina.

[0255] Addendum 45. The device of Addendum 24, wherein each of the plurality of optical elements comprises a lens that receives light emitted by a corresponding microdisplay and directs the resulting light beam into the pupil of the eye, where the light beam is focused to form an image in front of the retina.

[0256] Addendum 46. The device of Addendum 24, wherein the multiple light sources generate polychromatic illumination, and optionally the multiple light sources include multiple microdisplays that generate polychromatic illumination.

[0257] Clause 47. The device of clause 24, wherein the image is approximately 0.5 mm to 2.0 mm in front of the retina.

[0258] Clause 48. The device of clause 24, wherein the image has a resolution of at least 10 lp / mm, optionally at least 30 lp / mm.

[0259] Clause 49. The device of clause 24, wherein the image has a magnification of 200x or less, optionally 100x or less.

[0260] Clause 50. The device of clause 24, wherein the image has a depth of focus of 2.5 diopters or less, optionally wherein the depth of focus is about 0.9 mm or less.

[0261] Addendum 51. The device of Addendum 24, wherein the image is projected at an eccentricity in the range of about 7.5 degrees to about 45 degrees, optionally in the range of about 15 degrees to about 45 degrees.

[0262] Addendum 52. The device of Addendum 51, wherein the range is from about 15 degrees to about 30 degrees.

[0263] Addendum 53. The microdisplay has a resolution of about 100 cd / m 2 ~50,000cd / m 2 in the range of about 0.1 cd / m 2 ~10cd / m 2 25. The device of claim 24, wherein the pupil is illuminated with an illuminance in the range of.

[0264] Addendum 54. The device of Addendum 24, wherein the image is focused at a distance in front of the peripheral retina at a location, the image having a depth of focus and a spatial resolution, the depth of focus being less than the distance and the spatial resolution exceeding the spatial resolution of the peripheral retina at the location.

[0265] Addendum 55. The device of Addendum 24, further comprising a sensor for receiving input from the wearer when the contact lens is placed on the wearer's eye.

[0266] Addendum 56. A spectacle lens comprising a display, the display projects an image onto the periphery of the retina to reduce the worsening of myopia.

[0267] Addendum 57. The eyeglass lens of Addendum 56, wherein the display comprises a microdisplay.

[0268] Addendum 58. The eyeglass lens of Addendum 56, wherein the display comprises a picoprojector coupled to the eyeglass frame at a location corresponding to the wearer's temples.

[0269] Addendum 59. The eyeglass lens of Addendum 56, wherein the display comprises an eyepiece display.

[0270] Clause 60. The eyeglass lens of clause 56, wherein the display is configured to stimulate retinal ingrowth.

[0271] Addendum 61. The eyeglass lens of Addendum 56, wherein the display comprises a microdisplay and a micro-optical array.

[0272] Addendum 62. The eyeglass lens of Addendum 56, wherein the display enables a clear view of the real world across a field of view within a range of + / - 2.0 degrees to + / - 15 degrees, optionally within a range of about + / - 2.0 degrees to + / - 12.5 degrees.

[0273] Addendum 63. The eyeglass lens of Addendum 61, wherein the display projects an image of the light source of the microdisplay that is myopically defocused by an amount in the range of 2.0D to 7.0D, optionally in the range of 2.0D to 5.0D.

[0274] Addendum 64. The eyeglass lens of Addendum 56, wherein the display projects an image onto an outer region of the retina at an eccentricity relative to the fovea within a range of 15 degrees to 40 degrees, optionally within a range of 20 degrees to 30 degrees.

[0275] Addendum 65. The eyeglass lens of Addendum 56, wherein the lens comprises multiple ocular displays to effect binocular stimulation of the outer retina.

[0276] Clause 66. The eyeglass lens of clause 56, wherein the display transmits greater than 80% of light incident thereon over a field of view of + / - 5 degrees or more to the side and + / - 7 degrees vertically, optionally greater than + / - 12 degrees to the side and + / - 20 degrees vertically.

[0277] Addendum 67. A spectacle lens or device as described in any one of the preceding appendices, wherein the projected image moves to compensate for eye movement, and optionally the projected image moves to provide stimulation to overlapping regions of the periphery of the retina in response to eye movement.

[0278] Addendum 68. The eyeglass lens or device of any one of the preceding appendices, wherein the periphery of the retina constitutes an outer location of the retina, located away from the macula.

[0279] Addendum 69. The device of any one of the preceding appendices, further comprising a processor coupled to the plurality of light sources and controlling illumination of the plurality of light sources.

[0280] Addendum 70. The device of any one of the preceding appendices, further comprising wireless communication circuitry operatively coupled to the plurality of light sources and controlling illumination of the plurality of light sources.

[0281] Addendum 71. The device of any one of the preceding appendices, further comprising wireless communication circuitry operably coupled to a mobile device for a wearer to control illumination of the multiple light sources.

[0282] Addendum 72. The device of any one of the preceding appendices, further comprising wireless communication circuitry operably coupled to the processor for a healthcare provider to program illumination cycles and intensities of the multiple light sources.

[0283] Addendum 73. The device of any one of the preceding appendices, wherein the device does not include a contact lens.

[0284] While preferred embodiments of the present invention have been shown and described herein, it will be apparent to those skilled in the art that such embodiments are provided by way of example only. It is not intended that the present invention be limited by the specific examples provided in the specification. Although the present invention has been described with reference to the foregoing specification, the description and illustration of the embodiments herein are not meant to be construed in a limiting sense. Numerous variations, changes, and substitutions will now occur to those skilled in the art without departing from the present invention. Furthermore, it is to be understood that all aspects of the present invention are not limited to the specific depictions, configurations, or relative proportions set forth herein, which depend upon a variety of conditions and variables. It is to be understood that various alternatives to the embodiments of the present invention described herein may be employed in practicing the present invention. It is therefore contemplated that the present invention shall also cover any such alternatives, modifications, variations, or equivalents. The following claims define the scope of the present invention, and methods and structures within the scope of these claims and their equivalents are intended to be covered thereby.

Claims

[Claim 1] The invention described in this specification.

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