Apparatus for projecting an image onto a retina

Abstract

An apparatus for stimulating a retina includes 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 includes a depth of focus and a spatial resolution. The one or more images can be formed at a distance in front of the retina, at a distance behind 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.

Description

[0001] Related Applications

[0002] This application claims the benefit under 35 U.S.C. § 119(e) of the following U.S. Provisional Patent Applications: U.S. Provisional Patent Application No. 62 / 925,948, filed October 25, 2019, entitled “DEVICE FOR PROJECTING IMAGES ON THE RETINA”; U.S. Provisional Patent Application No. 62 / 907,496, filed September 27, 2019, entitled “DEVICE FOR PROJECTING IMAGES ON THE RETINA”; U.S. Provisional Patent Application No. 62 / 885,035, filed August 9, 2019, entitled “SPECTACLE LENSES WITH NEAR EYE DISPLAYS FOR PREVENTION OF MYOPIA PROGRESSION”; and U.S. Provisional Patent Application No. 62 / 881,123, filed July 31, 2019, entitled “SPECTACLE LENSES WITH NEAR EYE DISPLAYS FOR PREVENTION OF MYOPIA PROGRESSION”; the entire disclosures of which are hereby incorporated by reference.

[0003] BACKGROUND

[0004] Myopia, or nearsightedness, is a refractive error in which distant objects are focused in front of the retina. This can be related to the axial length of the eye. Generally, an increase in the axial length of the eye of 1.0 millimeter corresponds to an increase in myopia of 2.5 diopters (“D”).

[0005] Eyeglasses lenses, contact lenses, and refractive surgery can be used to treat refractive errors of the eye, such as myopia. While these methods can be effective in treating myopia, the eye can continue to grow in axial length, such that the degree of myopia continues to increase. The relatively high prevalence of myopia has prompted research to understand the underlying mechanisms of axial growth and to develop possible treatment methods for axial growth.

[0006] While it is known that myopia has a genetic component, the dramatic increase in the incidence of myopia cannot be explained by genetic factors alone; rather, they must simply be explained as the remarkable ability of the visual system to adapt to changing environmental conditions, particularly the shift in visual habits from distance to near and from open to enclosed spaces.

[0007] It is well known that the retinas of many species, including humans, react to defocused images and grow in order to minimize the blur caused by defocus. The mechanism of growth signal generation is still under investigation, but changes in choroidal thickness are an observable phenomenon of retinal tissue reacting to growth signals. Myopic defocused images cause the choroid to grow thicker, effectively shortening the axial length of the eye, while hyperopic defocused images cause the choroid to grow thinner, resulting in an increase in axial length. Work related to the present disclosure indicates that changes in axial length resulting from the retinal reaction to hyperopic blur or defocus can contribute to the development of myopia.

[0008] While defocus of images can play a role in changes in choroidal thickness and eye axial length, existing methods and devices are not ideally suited to address changes in retinal thickness and eye axial length. For example, pharmaceutical treatments have been proposed to treat myopia associated with axial length growth, and these treatments can have undesirable outcomes in at least some cases. While atropine and other muscarinic drugs can slow the progression of myopia, concerns about rebound effects after treatment and short-term and long-term side effects associated with long-term treatment can discourage widespread use of these drugs.

[0009] While animal studies have shown that refractive development and axial growth can be regulated by visual feedback associated with the effective refractive state of the eye, the methods and devices used in these animal studies are not well suited for treating myopia in humans.

[0010] Work related to the present disclosure indicates that the retinal shell becomes more aspherical as the eye becomes more myopic. Examples of the image shell on a myopic eye retina and conventional correction are described in Cooper, J, “A Review of Current Concepts of the Etiology and Treatment of Myopia” (Eye & Contact Lens, 2018; 44: p. 231). With conventional spherical lenses, light is focused on the center of the retina while the peripheral aspherical retina of a myopic eye receives light focused behind the retina, which can trigger a growth signal because the peripheral light is focused behind the retina, which is similar to an eye with insufficient axial length. Conventional spherical or curved lenses (e.g., contact or eyeglass lenses) generally cannot generate an image shell that matches the optimal shape needed to generate a refractive correction that will stop the growth signals that will make the retina more myopic. One approach is to provide an aspherical lens that focuses light to the peripheral region of the aspherical retina.

[0011] Prior refractive correction devices used to prevent myopia progression can produce less than ideal results in at least some cases. Providing proper focus at the peripheral retina with a refractive correction can require a highly aspheric optic that can be produced by a highly aspheric optic. Unfortunately, such aspheric optics can produce a central image with significant aberrations that, in at least some cases, compromise distance vision and reduce the wearer's visual quality. One approach is to limit the asphericity to about 2D or less in order to provide distance vision without significant aberrations to central vision, but such a limitation on asphericity also limits the amount of correction to the peripheral portions of the retina, which in some cases can result in less than ideal treatment.

[0012] A second approach taken by some prior art devices is to provide bifocal or multifocal optics that include a central optical zone for correcting refractive error only, while the peripheral zone typically has a greater positive power to form a myopic defocus image on the peripheral retina. Ray tracing analysis has shown that these bifocal optics can produce one or more foci at the fovea, thereby compromising image quality at the fovea.

[0013] Animal model studies, as well as clinical studies, have shown that the retina has the potential to distinguish "positive blur" and "negative blur," or image blur caused by myopic defocus and hyperopic defocus, by using longitudinal chromatic aberration as a guide, as the sign of longitudinal chromatic aberration will be opposite depending on whether the image blur is hyperopic or myopic. However, at least in some cases, prior clinical approaches can not have adequately addressed chromatic aberration to reduce myopia progression.

[0014] Accordingly, there is a need for new approaches to treating refractive error of the eye and promoting changes in the axial length and choroidal thickness of the eye to improve at least some of the limitations of prior approaches.

[0015] SUMMARY

[0016] In some embodiments, a device for stimulating a retina is configured to project one or more images onto the retina, the image falling outside the fovea. The stimulation can be configured to promote a change in axial length and / or choroidal thickness of the eye. The projected image can include a static image or a dynamic image, for example a dynamic image with a refresh rate in a range from 1 Hz to 500 Hz. The light can include monochromatic light or polychromatic light in a range from 400 nm to 800 nm. The one or more images can be configured in a variety of ways to have an image structure corresponding to information or content of the image, the information or content of the image being associated with a spatial frequency. In some embodiments, for example, the one or more images include a spatial frequency in a range from 1 cycle per degree to 180 cycles per degree, or from 1 cycle per degree to 30 cycles per degree, or from 1 cycle per degree to 10 cycles per degree, and a contrast in a range from 99.9% to 2.5%. The projected image can be projected onto the retina with an eccentricity relative to the fovea, and the eccentricity can be in a range from 5 degrees to 40 degrees. The projected image, for example with an annular pattern, can cover the entire retina in a specified eccentricity range, or the projected image can cover a portion of the retina in an eccentricity range. The stimulation can be continuous, periodic, or aperiodic. When the stimulation is periodic, the stimulation can last for a duration in a range from 1 second to 24 hours. The stimulation can be applied in a variety of ways, for example when the subject is awake or asleep, and combinations thereof. The retinal stimulation can be applied using a light projection system. The light projection system can be configured in a variety of ways, and adapted for use in conjunction with one or more of a plurality of devices. The projection optics described herein can be integrated into one or more of a projector, an ophthalmic device, a TV screen, a computer screen, a hand-held device such as a smartphone, a wearable device such as eyeglass lenses, a near-eye display, a head-mounted display, goggles, contact lenses, a corneal onlay, a corneal inlay, a corneal prosthesis, or an intraocular lens. For example, the projection optics can be incorporated in conjunction with combinations of these devices.

[0017] In some embodiments, a device for stimulating a retina includes a light source and optics to form an image in front of the retina, behind the retina, or on the retina with one or more of an appropriate resolution, depth of focus, or diffraction. The image formed on a region of the retina can include a finer resolution than the resolution of the retina at that region, such as the highest resolution of the retina at that region. The light beams can be directed to the region of the retina at an angle relative to the optical axis of the eye so as to illuminate an outer portion of the retina away from the fovea with a finer resolution than the corresponding location of the retina. The depth of focus can be configured to illuminate the retina with an appropriate amount of blur of the image on the retina, and the diffraction size of the light spot can be appropriately adjusted to provide a finer resolution than the resolution of the retina for the image formed in front of the retina.

[0018] According to some embodiments, a device for stimulating a retina includes micro-displays positioned away from a center of a lens and toward a periphery of the lens, where each micro-display is coupled to a micro-lens array positioned behind the micro-display. The micro-displays can include OLED (organic light emitting diode) or micro-LED arrays. The micro-lens array can be optically coupled with the displays to effectively collect light from the micro-displays and substantially collimate and / or converge the light before projecting the light into an entrance pupil. The images produced by these displays can be myopically or hyperopically defocused and placed symmetrically in multiple regions on the retina, such as in four quadrants (nasal-inferior, nasal-superior, temporal-inferior, and temporal-superior). The micro-displays can be positioned away from an optical center of the lens by a distance in a range from 1.5 mm to 4.0 mm, such as 2.5 mm to 3.5 mm. A central optical zone 14 of the lens can be configured to provide emmetropia vision for the wearer and can have a diameter in a range from 3.0 mm to 5.0 mm. Each micro-display can generate a retinal image with an appropriate shape, such as a circular or arc shape, and the retinal image is at an angle of about 20 degrees to 60 degrees relative to the fovea. In some embodiments, the retinal image formed at the peripheral retina has a decentration in a range from 7.5 degrees to about 45 degrees, or 15 degrees to about 45 degrees, or 15 degrees to 40 degrees (e.g., in a range from 15 degrees to 30 degrees, 20 degrees to 30 degrees, or 25 degrees to 30 degrees). The lens can include an electronic control system mounted with the micro-displays on a flexible transparent material sheet, such as plastic, and other components.

[0019] In some embodiments, the microdisplay includes an OLED having a pixel size in a range from 2.0 microns (micron) to 5.0 microns, having a pitch in a range from 3.0 microns to 10.0 microns. In some embodiments, the microdisplay includes an OLED having a pixel size in a range from 5.0 microns (micron) to 50.0 microns, having a pitch in a range from 10.0 microns to 100.0 microns. In some embodiments, the microdisplay embedded in the lens includes micro-LEDs that illuminate an object, such as a thin film placed in front of the microdisplay and towards the eye. The film can be transparent or translucent, including a printed pattern that can be a Fourier transform of an image designed to be projected onto the retina. The microdisplay can include a multi-color or a single-color microdisplay. A multi-color image can be formed by RGB pixels in an OLED or different color micro-LEDs organized in an array so as to form an RGB display. In some embodiments, the wavelength for retinal stimulation is in a range from about 450 nm to about 560 nm (in some embodiments, from about 410 nm to about 560 nm), and can be close to the peak wavelength of 500 nm that stimulates rod cells in the eye, although other wavelengths can also be used. In some embodiments, the chromaticity of the light source includes violet light, including wavelengths in a range from 400 nm to 450 nm.

[0020] In some embodiments, the optical configuration includes one or more light sources coupled to one or more projection optics, including one or more of a collimating lens, a compound lens such as a Gabor lens, a prism, a prism array, 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 so as to project an image of the light source in front of, behind, or above the peripheral retina. In some embodiments, the optical configuration is placed 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 are configured to provide additional focusing to provide a defocused image of the microdisplay on the retina. In some embodiments, the amount of defocus is in a range from about 2.00 diopters (D) to 6.00 D, and can be in a range from about 2.0 D to 4.0 D.

[0021] In some embodiments, a spectacle lens is configured with a near-eye display that projects a 2.0D to 5.0D or 2.0D to 7.0D myopic defocus image at the peripheral retina while maintaining central vision. In some embodiments, a device comprising a pair of spectacle lenses is configured with a near-eye display that projects a pair of 2.0D to 5.0D or 2.0D to 7.0D myopic defocus images at the peripheral retina while maintaining central vision. Each optical of the device can be coupled to the near-eye display to project one or more myopic defocus images at the peripheral retina while the optical center of the spectacle lens optic provides the wearer with the required refractive correction for distance vision. The optical can be configured to provide the refractive correction so as to allow for comfortable and clear viewing of the real world at all object distances while the display projects a 2.0D to 5.0D or 2.0D to 7.0D myopic defocus image to the peripheral portion of the retina.

[0022] In some embodiments, a spectacle lens is configured to project a myopic defocus image at the peripheral retina while maintaining good focus at the central retina. In some embodiments, a spectacle lens is configured to provide a light field in which the refractive power of the lens varies with the gaze direction and the object distance across the spectacle lens optic body. In some embodiments, a spectacle lens is configured to provide a match between the divergence, the image magnification, and the refractive correction. In some embodiments, near vision is generally associated with lower gaze angles (downgaze) and the refractive power of the multi-focal or progressive spectacle lens optic is increased downwardly. In some embodiments, the spectacle is configured for a wearer that can accommodate a spectacle providing less positive power. Additionally, the optical design of the binocular optics can be adjusted to facilitate binocular summation when performing conjugate eye movements. In some embodiments, the unmodified region of the spectacle lens optic is disposed around the optical center of the spectacle lens optic with a region diameter of about 8mm to 15mm, preferably 10mm to 12mm. In some embodiments, the unmodified region of the spectacle lens optic is disposed around the optical center of the spectacle lens optic with a region diameter preferably of 10mm to 15mm.

[0023] In some embodiments, a near-eye display includes micro light sources (such as organic light emitting diodes ("OLEDs"), transparent organic LEDs ("TOLEDs"), or i-LEDs), and a micro-lens array to substantially collimate light emitted from the light sources and direct the light to the pupil of the eye. Alternatively or in combination, a micro-mirror array can be used to collimate light emitted from the light sources and direct it to the pupil of the eye. In some embodiments, the light sources are mounted on a transparent substrate (e.g., TOLEDs), while in some embodiments, the light sources can be mounted on a non-transparent substrate such as silicon. The light sources can include active matrix or passive matrix. These components can be held together in a transparent hermetic package. In some embodiments, the hermetic package can be conformal, including a multi-layer film with a total thickness in a range from 5 microns to 25 microns (e.g., from 10 microns to 15 microns). The device can also include components that can monitor eye movements, such as a gaze tracker. In some embodiments, the gaze tracker is configured to position a point on the eyeglass lens optics sheet corresponding to a point of interest at which the optical axis of the eye intersects the optics for the particular position of the eye when the eye performs a pursuit eye movement such as tracking a moving object. In some embodiments, the eye movements can be monitored and followed by an eye tracker that can include a coil embedded in the eyeglass frame that senses the motion of the eye during the eye movement by development of a transient magnetic field, for example, by the motion of a coil such as one within a contact lens worn on the eye. In some embodiments, a retinal image formed by light rays from the display is myopically defocused 2.0D to 5.0D or 2.0D to 7.0D in front of the retina and falls on an outer portion of the retina, forming an image in front of the retina. While the image can be formed in front of the retina in many ways, in some embodiments, the image is formed about 15 degrees to 40 degrees eccentric to the fovea. In some embodiments, the image is formed about 5 degrees to 40 degrees eccentric to the fovea. BRIEF DESCRIPTION OF DRAWINGS

[0025] A better understanding of the features, advantages, and principles of the present disclosure will be obtained by reference to the following detailed description and drawings that

[0026] Figure 1 A soft contact lens is shown in accordance with some embodiments;

[0027] Figure 1A And Figure 1B Eyeglasses suitable for use in conjunction with the present disclosure are shown in accordance with some embodiments;

[0028] Figure 2AAn OLED microdisplay embedded in a soft contact lens according to some embodiments is shown, the OLED microdisplay being optically coupled to a microlens array for projecting a myopic defocused image onto the peripheral retina of the wearer;

[0029] Figure 2B A soft contact lens according to some embodiments is shown, the soft contact lens including multiple light sources and optics as well as associated circuitry;

[0030] Figure 2C As shown Figure 2B The diagram shows the system diagram of the functions of the contact lens components.

[0031] Figure 3 An optical configuration according to some embodiments is shown, wherein the optical path length is increased by using two mirrors to fold back the optical path;

[0032] Figure 4 Illustrations are shown according to some embodiments Figure 3 The optical configuration shown is a ray-tracing simulation in which the LiouBrennan eye model has been used to calculate retinal images;

[0033] Figure 5A and Figure 5B It shows the result of Figure 3 Analysis of the quality of retinal images generated by the optical configuration;

[0034] Figure 6 It shows Figure 3 Depth of focus analysis of the optical configuration shown;

[0035] Figure 7 The analysis is shown Figure 6 MTF;

[0036] Figure 8A and Figure 8B An optical configuration according to some embodiments is shown, including a lens that focuses light onto the retina;

[0037] Figure 9 The diagram illustrates the use of some embodiments of the invention. Figure 8A and Figure 8B Analysis of the quality of retinal images generated by the optical configuration shown;

[0038] Figure 10 It shows the Figure 8A and Figure 8B Analysis of the depth of focus of the optical configuration shown;

[0039] Figure 11A and Figure 11B An optical tube for increasing the optical path length is shown according to some embodiments;

[0040] Figure 12 A soft contact lens with embedded light sources, optics, and electronics is shown in accordance with some embodiments;

[0041] Figure 13 A ray tracing simulation of a peripheral retinal image formed by a combination of micro light sources and micro optics is shown in accordance with some embodiments;

[0042] Figure 14 Four object points used to simulate image quality using ray tracing for a light source comprising four simulated object points are shown in accordance with some embodiments;

[0043] Figure 15 Quality of a peripheral image generated by a reflective optic where the modulation transfer function (MTF) of all object points is substantially uniform is shown in accordance with some embodiments;

[0044] Figure 16 Depth of focus of a peripheral image formed by a reflective optic is shown in accordance with some embodiments;

[0045] Figure 17 The effect of myopic blur on the image resolution of a peripheral retinal image formed by a reflective optic is shown in accordance with some embodiments, as measured by the change in MTF amplitude at a single spatial frequency (20 / 200 or 10 line pairs per mm “lp / mm” or 10 arc minutes) as a function of the myopic defocus amplitude of the reflective optical design;

[0046] Figure 18 MTF plots of a retinal image formed by a refractive optic for Figure 14 four object points shown in accordance with some embodiments;

[0047] Figure 19 Depth of focus of an image formed by a refractive optic is shown in accordance with some embodiments;

[0048] Figure 20 MTF calculated for a single spatial frequency (20 / 200 or 10 lp / mm, or 10 arc minutes) as a function of myopic defocus is shown in accordance with some embodiments;

[0049] Figure 21 MTF plots for four object points in Figure 14 a micro light guide embodiment where there is a significant difference in image quality between the sagittal and tangential planes, indicating asymmetric aberrations, are shown in accordance with some embodiments;

[0050] Figure 22Focal depths of peripheral retinal images projected by a light guide optic are shown according to some embodiments;

[0051] Figure 23 MTF curves at a single spatial frequency (20 / 200) plotted against the myopic defocus amplitude of peripheral images on the retina for embodiments with a light guide are shown;

[0052] Figure 24 A comparison of focal depths of peripheral images generated by three projection systems including a refractive optic, a reflective optic, and a light guide optic according to some embodiments is shown;

[0053] Figure 25 Focal depths of retinal images generated by a reflective optical design according to some embodiments are shown, and

[0054] Figure 26 MTF values at a single spatial frequency plotted against the myopic defocus amplitude of peripheral images created by a reflective optical design according to some embodiments are shown. Figure 25

[0055] DETAILED DESCRIPTION

[0056] The disclosed methods and devices can be configured in a variety of ways to provide retinal stimulation as described herein. The disclosed methods and devices are well suited for combination with many existing devices, such as one or more of an ophthalmic device, a TV screen, a computer screen, a handheld device, a mobile computing device, a tablet computing device, a smart phone, a wearable device, an eyeglass frame, an eyeglass lens, a near-eye display, a head-mounted display, eyewear, contact lenses, an implantable device, a corneal onlay, a corneal inlay, a corneal prosthesis, or an intraocular lens. Although specific reference is made to eyeglasses and contact lenses, the disclosed methods and devices are well suited for use with any of the aforementioned devices, and one of ordinary skill in the art will readily understand how one or more components of the disclosure can be interchanged between devices based on the teachings provided herein. For example, although specific reference is made to a contact lens having a projection optic, a light source, and circuitry to stimulate the retina away from the fovea, the projection optic, light source, and circuitry can be incorporated into one or more of an ophthalmic device, a TV screen, a computer screen, a handheld device, a mobile computing device, a tablet computing device, a smart phone, a wearable device, an eyeglass frame, an eyeglass lens, a near-eye display, a head-mounted display, eyewear, contact lenses, an implantable device, a corneal onlay, a corneal inlay, a corneal prosthesis, or an intraocular lens in order to provide retinal stimulation as disclosed herein.

[0057] ​Methods and apparatus for retinal stimulation as described herein can be configured in a variety of ways, and can include one or more attributes that encourage a user to accept treatment. For example, retinal stimulation as described herein can be combined with the display of a game to encourage a user to wear a treatment device. In some embodiments, retinal stimulation can be combined with another stimulus, such as an emoji, to encourage a user to wear a device for treatment.

[0058] A retinal stimulation device can include a global positioning system (GPS) circuit for determining the location of the wearer, and an accelerometer for measuring body motion, such as head motion. The retinal stimulation device can include a processor coupled to one or more of the GPS or accelerometer to receive and store measurement data. The retinal stimulation device can include a communication circuit, such as a wireless communication circuit, e.g., Bluetooth or WiFi, or a wired communication circuit, e.g., USB, to transmit data from the device to a remote server, such as a cloud-based data storage system. Such transmission of data to a remote server can allow for remote monitoring of a wearer’s treatment and compliance. In some embodiments, the processor includes a graphics processing unit (GPU). The GPU can be used to efficiently and quickly process content from the web for use in forming stimuli as described herein.

[0059] 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 stimulation signal.

[0060] In some embodiments, the one or more projection optics are configured to project the defocused images onto the retina away from a central field including the macula in order to stimulate an increase in choroidal thickness. In some embodiments, the one or more projection optics are configured to project the defocused images onto the retina away from a central field including the macula in order to stimulate a transient increase in choroidal thickness. The one or more projection optics can be configured to stimulate the retina without reducing central vision and the quality of the corresponding images formed on one or more of the foveal or macular region of the retina. In some embodiments, the one or more projection optics do not reduce the image-forming properties of vision correction optics for correcting refractive errors of the wearer. The correction optics can include one or more of a contact lens, an eyeglass 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 include an optical display such as a micro-optical display and the one or more projection optics include a micro-optical array. These components can be mounted on a flexible printed circuit board (“PCB”) substrate for supporting the electronic and optical components. In some embodiments, the micro-display is optically coupled to a micro-optical array that substantially collimates and focuses light emanating from the micro-display. The micro-display can include miniaturized pixels that each range in size from 2 microns to 100 microns. For example, the micro-display can be coupled to and supported by a body of the correction optics such as a contact lens or an eyeglass lens. In some embodiments, the micro-display is coupled to and supported by one or more of an intraocular lens, a corneal prosthesis, a corneal onlay, or a corneal inlay. For example, the optical configurations described herein with reference to a contact lens can be similarly used with one or more of an intraocular lens, a corneal prosthesis, a corneal onlay, or a corneal inlay.

[0061] In some embodiments, 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 embedded in an outer surface of a pair of eyeglasses lenses. In some embodiments, the projection optics include a miniature projector mounted on a temple of an eyeglasses frame. In some embodiments, the projection optics are optically coupled with one or more optical fibers that deliver the projected image to an eyeglasses optic and direct the projected image to the pupil of the eye, for example, with a partially transmissive mirror. In these embodiments, an eye tracker can be configured to monitor eye movements so that activation of pixels in the microdisplay can be programmed to compensate for eye movements recorded by the eye tracker. In some embodiments, the subject wears a contact lens that provides refractive correction for the subject's eye. A wire or a magnetic material is embedded in the contact lens that generates a magnetic field in a search coil mounted in an inner surface of the frame of the eyeglasses when eye movement occurs. In some embodiments, the magnetic field is analyzed with a processor to determine the start and stop points of the eye and the time it takes to perform the eye movement. In some embodiments, the microdisplay and the circuitry coupled to the display are configured to respond to the eye movement and selectively activate a different plurality of pixels within the appropriate time in response to the eye movement. The time to selectively switch to the second plurality of pixels in response to the eye movement can be less than 100 milliseconds, for example, less than 20 milliseconds.

[0062] In some embodiments, the microdisplay and the micro-optics array are mounted in close proximity to each other on the same corrective optics, separated by a fixed distance, so as to project a bundle of light rays into the pupil of the eye in an orientation to form a myopic defocus image at a desired location on the retina, as described herein. In some embodiments, one or more projection optics are mounted on or in one or more corrective optics, such that light from the projection optics is refracted through the corrective optics. The corrective optics refract the light from the projection optics to be converging or diverging to assist in emmetropization, so that the micro-optics array can provide a desired magnitude of additional optical power, which can be positive or negative, depending on the magnitude and sign of the defocus desired. The microdisplay can be, for example, monochromatic or multichromatic. For example, the microdisplay can have an illuminance in a range from 1 nit to 10,000 nits or 10 nits to 1000 nits, or from 100 lux to 5,000 lux. In some embodiments, the microdisplay can have an illuminance in a range from 100 nits to 50,000 nits, or from 50 lux to 5,000 lux, for example. In some embodiments, the microdisplay is positioned off-center relative to the optical center of the corrective optics to a distance from the center of the corrective optics in a range from 1.0 mm to 4.0 mm. In some embodiments, the microdisplay forms an extended pixel array characterized by a pixel size and a pixel pitch, where the pixel size and the pixel pitch together correspond to a fill factor of the microdisplay. As described herein, for example, the pixel size can be in a range from 2 microns to 100 microns, and the pixel pitch can be in a range from 10 microns to 1.0 mm. The corresponding fill factor can be in a range from 0.1% to 10%. In some embodiments, the pixel array is optically coupled with the micro-optics array so as to substantially collimate and focus light from the pixels. In some embodiments, the layers of the microdisplay and the layers of the micro-optics array are encapsulated in a substantially transparent medium configured to reduce scattering of light. For example, the encapsulated image delivery system including one or more light sources and one or more projection optics can be subsequently coated with a conformal, hermetic, transparent multi-layer coating.

[0063] In some embodiments, the microdisplay can be mounted on a corrective optics such as an eyeglass lens, while the micro-optics array can be mounted on a second corrective optics such as a contact lens, a corneal onlay, or a corneal inlay. Alternatively or in combination, an augmented reality (AR) or virtual reality (VR) display can be used to project the defocus image onto the retina. The AR or VR device can be mounted on an eyeglass frame, goggles, or a head-mounted display. Refractive correction can be provided by the eyeglass lens or the contact lens, while the optics of the micro-optics array coupled to the AR or VR device provide the defocus.

[0064] In some embodiments, the projected defocused image can be provided by a screen including one or more of an LCD screen, a screen driven by OLED (Organic Light Emitting Diode), a screen driven by TOLED, a screen driven by AMOLED, a screen driven by PMOLED, or a screen driven by QLED. For example, the screen can appear to the subject at a far distance of at least 6 meters or more.

[0065] The stimulation can be configured in a variety of ways, and can include monocular stimulation or binocular stimulation.

[0066] The micro-optics array can be configured in a variety of ways, and can include one or more of a lenslet array, a compound lens (such as a Gabor lens) array, one or more mirrors, prisms, light pipes or light guides or waveguides.

[0067] In some embodiments, the projected image includes image structure content configured to provide a range of spatial frequencies, for example in a range from 2 cycles per degree to about 60 cycles per degree. In some embodiments, the projected image includes image structure content configured to provide a range of spatial frequencies between 2 cycles per degree and about 30 cycles per degree. Work related to the present disclosure indicates that the ability of the peripheral retina to detect blur is higher than its ability to resolve images. The size and shape of the projected image can be in a range from 100 microns to 2.5 mm, for example, towards an angular range of from 15 degrees to 360 degrees or from 5 degrees to 360 degrees relative to the fovea. The location of the image can be in a range of 5 degrees to 30 degrees of eccentricity relative to the fovea, for example in a range of 12 degrees to 30 degrees. Alternatively, the projected image can cover the entire retina, for a pan-retinal defocus treatment.

[0068] In some embodiments, the luminance of the projected image is in a range from 1 Troland to 250 Troland. In some embodiments, the image luminance can be adjusted based on the luminance of ambient lighting. The contrast range of the projected image can be in a range from 99.9% to 2.5%, for example in a range from 99.9% to 10%.

[0069] The projection of the defocused image as described herein can be for any appropriate amount of time, for example, a substantial portion of a day (e.g., 8 hours or more), and the stimulation can be repeated at approximately the same time each day so as not to interfere with the circadian rhythm. The duration of the projected image can be as short as 15 minutes, for example, repeated throughout the day at hourly intervals. The image can be projected continuously in a range from 15 minutes to 12 hours each day. The stimulation can be provided for a period of 1 day to 3 years, or for as long as the treatment is beneficial.

[0070] According to some embodiments, the soft contact lens comprises peripheral micro-displays, each facing the eye side through a micro-lens array. The micro-displays can comprise OLED (Organic Light Emitting Diode) or micro-LED arrays. The light emitted by these displays is typically Lambertian. The micro-lens array is optically coupled with the display so they can efficiently extract light from the micro-display, collimating and focusing the light before projecting it to the entrance pupil. In some embodiments, the virtual images created by these displays will be myopically defocused and will be placed symmetrically in the four sub-zones (nasal-lower, nasal-upper, temporal-lower and temporal-upper). In some embodiments, the micro-displays will be located at a distance ranging from 1.5 mm to 4.0 mm, preferably from 2.5 mm to 3.5 mm, away from the optical center of the lens. The central optics of the contact lens can be chosen to make the wearer as close to emmetropia as possible and can have a diameter ranging from 3.0 mm to 5.0 mm. In some embodiments, the shape of each micro-display will be circular, rectangular or arcuate and the area of each micro-display will range from 0.01 mm 2 to 8.0 mm 2 , for example from 0.04 mm 2 to 8.0 mm 2 , for example from 1 mm 2 to 8 mm 2 , or preferably from 1.0 mm 2 to 4.0 mm 2 . In some embodiments, each of the plurality of micro-displays comprises a light source, a backplane and associated electronics having dimensions and shapes as described herein. The contact lens will have an electronic control system and the micro-displays mounted on a flexible transparent plastic sheet. The electronic system can comprise an ASIC or microcontroller, a rechargeable lithium-ion solid-state battery, a voltage ramp module (e.g. a buck-boost converter), a flash memory and EEPROM, an RFID module for providing wireless recharging, or preferably an antenna disposed radially along the edge of the contact lens and any combination thereof. The contact lens comprises a biocompatible material such as a soft hydrogel or silicone hydrogel material and can comprise any material composition that has been proven to be compatible with the continuous wear of a contact lens on the eye.

[0071] In some embodiments, the virtual images are focused at a target distance from the peripheral retina, equivalent to myopic defocus. The light rays forming these images do not come from the external environment but from the micro-displays themselves, so the optics of the micro-lens array can be designed individually to handle the light rays emitted from the micro-displays. The area of each of these micro-displays and the area of the micro-lens array in front of each micro-display are small, so the occlusion of the real image is also small, as Figure 1A -B andFigure 2A -C as shown.

[0072] The apparatus as described herein can set and test such parameters for a single patient and then give each caregiver considerable flexibility in refining the preferred parameters of treatment based on observations of the patient's response.

[0073] Some embodiments include a contact lens having a diameter of 14.0 mm with a 1.0 mm peripheral zone and a 6.0 mm inner diameter and a 12.0 mm outer diameter peripheral zone 16. The overall diameter of the lens can be in the range of 13.0 mm and 14.5 mm, preferably in the range of 13.5 mm and 14.5 mm. The central optical zone 14 is designed to cover the pupil of all wearers under all lighting conditions, so its diameter should be in the range of 5.0 mm and 8.0 mm. The peripheral or blending zone is designed primarily to provide a good match to the cornea, including good centration and minimal decentration. The central optical zone 14 is designed to provide emmetropic correction to the wearer and can provide both spherical and astigmatic correction Figure 1 ). The design of contact lenses suitable for incorporation in accordance with embodiments disclosed herein is described in Douthwaite, D. A., "Contact lens optics and lens design", 3rd edition, 2006; ISBN 978-0-7506-88-79-6; Butterworth-Heinemann.

[0074] In some embodiments, the inner surface of the contact lens is embedded with a set of four micro-displays that are coupled on the eye side with a micro-lens array of the same size. The function of the micro-lens array is to collimate the light emitted by the micro-displays and focus that light on a focal point designed to be in front of the eye to provide hyperopic defocus. The micro-displays can be sized in a number of ways, and the area of each of these micro-displays is only about 0.04 mm 2 to 2 mm 2 , for example 1 mm 2 to 2 mm 2 , so that in some embodiments these displays cover less than 1% of the optical piece of the contact lens. Each display will generate an illuminance of approximately 30-50 cd / m 2 or more, sufficient to form a relatively bright image at the focal point of each of these micro-displays. For example, the focal images will appear about 1.5 mm - 2.5 mm in front of the peripheral retina, as they will be designed to be about 2.0 D to 5.0 D myopic, for example 2.0 D to 4.0 D, or preferably 2.5 D to 3.5 D.

[0075] In some embodiments, the microdisplay can be an OLED with pixel sizes 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 embedded in the contact lens as described herein will consist of microLEDs that illuminate an object such as a thin film placed in front of the eye side. The microdisplay can be multicolored or it can be monochromatic. Multicolor images are formed by RGB pixels in the OLED or by different colored microLEDs organized in an array to form an RGB display. There is a lack of data on wavelength dependence of the axial length change for hyperopic or myopic images projected at the peripheral retina. The preferred wavelength for stimulating axial length change is 500 nm, the peak wavelength that stimulates the rod cells in the eye, although other wavelengths can also be used.

[0076] Based on the preclinical data available in animal models, the length and duration of the peripheral stimulation can be determined (e.g., optimized). For example, some studies suggest that the change in axial length in animal models can be obtained by repeated application of defocused stimulation, rather than by a single duration period of equivalent duration of the applied defocus. Examples of studies that are applicable to the use of the information on the change in illumination in the axial length incorporated in accordance with the embodiments disclosed herein include: Wallman, J. et al., “Homeostasis of eye growth and the question of myopia”, published in Neuron, 2004; 43: p. 447; 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”, published in IOVS 2014; 55: p. 6767; and Hammond, D. S. et al., “Dynamics of active emmetropisation in young chicks - influence of sign and magnitude of imposed defocus”, published in Ophthalmic Physiol Opt. 2013; 33: p. 215-222.

[0077] Work related to the present disclosure indicates that the duration and profile of the applied peripheral myopic defocus will depend on the individual physiology and the exact shape of the retina. One embodiment includes a reprogrammable MCU or ASIC that controls the operation of the microdisplay, and a real-time clock that enables the caregiver to adjust the treatment duration and cycle throughout the course of treatment. This embodiment also enables the caregiver to test whether the night-time stimulation (a sustained or repeating sequence of short pulses) is effective for the particular individual.

[0078] In some embodiments, the electronic components are populated on a flexible thin film, and the interconnects and electrical buses are deposited on the thin film by vapor deposition or 3D printing processes. In some embodiments, the electronics and microdisplay are further coated with a flexible stack of thin barrier films, such as a stack of Paralyne C and SiOx films with a total thickness of 5-10 microns developed by Coat-X, a company located in Nyon, Switzerland.

[0079] Some embodiments of the device deploy a set of microdisplays, one to eight microdisplays, each of which is circular or arcuate, and they are disposed radially on the inner surface of the contact lens, all at the same distance from the optical center of the lens. In one embodiment, they can be monochromatic. In another embodiment, they can be designed to provide white light output. In a third embodiment, they can be designed to output illumination that matches the sensitivity of the retina. These microdisplays are operated and controlled by a reprogrammable microcontroller (MCU) or ASIC.

[0080] In some embodiments, the contact lens is worn during sleep, and the microdisplays are programmed to operate only when the wearer is asleep. This reduced-axial-length programmed stimulation minimizes the disruption to daily activities, including reading and computer work. The contact lens can even be removed during daytime activities, while it is fitted on the cornea just before sleep. Other embodiments can utilize other programming algorithms, such as a combination of daytime and nighttime stimulation.

[0081] In some embodiments, the contact lens can be a daily disposable lens, obviating the need for disinfecting and cleaning or recharging the lens. Another embodiment includes a contact lens in the form of a scheduled replacement.

[0082] In some embodiments, each microdisplay (1 mm 2 to 4 mm 2 ) will consume approximately 10 microwatt-hours of electrical energy. In these embodiments, a set of four microdisplays can use about 125 microwatt-hours of electricity in a 2-hour operation, so the total daily energy consumption for this design would be expected to be 0.2 milliwatt-hours. In some embodiments, each microdisplay includes a 0.04 mm 2 to 4 mm 2The power supply can be a solid state battery that is small enough to fit within the cross-sectional area of the lens and consumes about 10 microwatts of power. In some embodiments, the power is provided by a rechargeable solid state lithium ion battery. A bare die solid state rechargeable lithium ion battery sold by Cymbet Corporation can be mounted on the same flexible substrate as the electronics of the lens. For example, a 50 uAH rechargeable lithium ion solid thin film battery is 5.7 mm x 6.1 mm x 0.200 mm in size (Cymbet Corporation CBC050). In some embodiments, the battery includes a mass sufficient to stabilize the contact lens. For example, the battery can be positioned on the lower portion of the lens so as to stabilize the lens with gravity. The battery positioned on the lower portion can include a mass sufficient to reduce rotational motion, such as rotation, when the wearer blinks.

[0083] In some embodiments, the electronic contact lens projects a myopic defocused image of 2.0D to 5.0D or 2.0D to 7.0D at the retinal periphery while maintaining good vision in the center.

[0084] In some embodiments, the electronic soft contact lens includes a micro light source and micro-scale optics embedded in the periphery of the lens optical piece. The contact lens optical piece can be designed to provide good vision at the central retina when an external light source projects a myopic defocused image at the external portion of the retina. In some embodiments, the light source includes a micro display. In some embodiments, the external image formed in front of the retina can stimulate the retina to move forward, reduce the axial length, and deepen the vitreous chamber. In some embodiments, the contact lens is configured to one or more of reduce myopia progression, substantially stop myopia progression, or reverse myopia in an eye in which the lens is worn. In some embodiments, the contact lens can be configured for extended wear and, for example, replaced once a month. The contact lens can be replaced more frequently or less frequently, for example, once a week, or once every three months. In some embodiments, the contact lens is designed to be worn by teenagers and young people who can be at greater risk of myopia progression than other age groups.

[0085] In some embodiments, the peripheral image has a myopic defocus amount in a range from about 2.0D to about 7.0D, such as from 2.0D to about 5.0D or from about 2.5D to about 5D. Based on the teachings disclosed herein, one of ordinary skill in the art can conduct studies, such as clinical studies, to determine appropriate amounts of defocus, illumination intensity, and illumination time. In some embodiments, one or more of the amount of defocus, retinal location of retinal illumination, or illumination time can be customized to the individual, such as in response to physiological characteristics of the individual patient. The duration of treatment can be in a range from 1 year to 3 years, such as about 2 years. In some embodiments, the treatment is performed with a number of lenses in a range from about 10 lenses to about 40 lenses, such as from about 10 lenses to about 30 lenses. During the treatment, the prescription of the optical zone 14, including the central lens optic, can change over time, and the prescription of the contact lens can be changed as appropriate. The contact lenses as disclosed herein can also be worn subsequently as needed, such as if the progression of myopia resumes.

[0086] An electronic contact lens can be configured in a variety of ways to correct refractive errors of a wearer. In some embodiments, the contact lens includes a plurality of micro-displays that emit light near the periphery of the optical zone 14 of the contact lens, a plurality of micro-optics for collecting, collimating, and focusing light rays emitted from the light sources, a miniaturized rechargeable solid-state battery (such as a lithium-ion solid-state battery) for providing power to the light sources, an antenna for wirelessly receiving power to recharge the battery, and a microcontroller for controlling actuation and control functions, and a memory for storing data or software instructions.

[0087] In some embodiments, the peripheral image includes a peripheral image located outside the macula, such as in a range from about 20 degrees to about 30 degrees eccentric to the fovea.

[0088] The contact lens can be configured with a plurality of optics, such as micro-optics, in a variety of ways to collect light from a plurality of light sources, such as micro light sources, and form an image in front of the peripheral portion of the retina, such as in front of the peripheral portion of the retina. In some embodiments, the plurality of optics includes one or more of a light pipe and a reflective component, such as a mirror, for example a micro mirror.

[0089] The devices as described herein can be used to treat the progression of refractive errors, such as myopia. In some embodiments, each caregiver has considerable flexibility in setting and testing parameters for individual patients, and then refining preferred parameters of the treatment based on observations of the patient’s response.

[0090] In some embodiments, the optical design of the refractive properties 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 to best correct for distance images in the fovea, while providing images at the periphery of the retina in front of the visual shell of the contact lens optic, thereby reducing the development of refractive errors. In some embodiments, the light source can include a surface area of the optical surface of no more than 2 mm 2 and the size of the optical surface used to correct for refractive errors can be in the range from about 25 mm 2 to about 50 mm 2 , which can reduce the impact of the light source on vision. The intensity of the peripheral images can be provided independently of the ambient lighting level, and the intensity of the light source can be adjusted over several orders of magnitude by selecting a light source of appropriate power. The soft contact lens can be configured to provide an appropriate amount of illumination in response to input from the wearer or a health care provider.

[0091] Figure 1 A microdisplay 12 embedded in a lens such as a contact lens 10 as described herein is shown. Although reference is made to a contact lens, the lens 10 can include a lens of one or more of a projector, an ophthalmic device, a TV screen, a computer screen, a hand-held device such as a smartphone, a wearable device such as glasses, a near-eye display, a head-mounted display, goggles, a contact lens, a corneal onlay, a corneal inlay, a corneal prosthesis, or an intraocular lens.

[0092] The soft contact lens 10 includes an optical zone 14 configured to provide distance vision correction to the wearer, for example with a visual acuity of 20 / 20 or better. The optical zone 14 can include a span such as a diameter or radius 15, which can include any suitable size such as a radius of about 3 mm. As described herein, the microdisplay 12 can be configured to provide images in front of the peripheral portion of the retina. As described herein, this configuration can allow the user to have good visual acuity while receiving treatment from images focused in front of the retina. The microdisplay 12 can be located outside of the optical zone 14, or inside of the optical zone 14. Each of the microdisplays 12 can include a maximum span such as a diameter 19, which can be any suitable size, for example about 1 mm.

[0093] The micro-displays 12 can include micro-LEDs that illuminate an object, such as a thin film placed in front of the micro-displays 12 on the side of the eye. The light emitted by these micro-displays 12 can be Lambertian light and is directed to optical elements, such as lenses, to direct the light beams to the retina. The contact lens 10 includes a diameter 13 suitable for placement on the eye. For example, the contact lens 10 can include a diameter in the range of approximately 10 mm to 15 mm, such as 14.0 mm. The contact lens 10 can include a plurality of embedded micro-displays 12. Each of the plurality of micro-displays 12 can be optically coupled to an optical configuration that collects light emitted by the micro-displays 12 and projects an image onto or in front of the wearer’s retina with a specified eccentricity. Each of the displays 12 can generate illumination in the range of approximately 1 cd / m 2 to approximately 50 cd / m 2 In some embodiments, each of the displays 12 can generate illumination in the range of approximately 50 cd / m 2 to approximately 50000 cd / m 2 or from approximately 100 cd / m 2 to approximately 50000 cd / m 2 The amount of illumination is sufficient to form a relatively bright image at the focal point of each of these micro-displays 12.

[0094] In some embodiments, the amount of illumination is between a photopic illumination level and a mesopic illumination level and between a rod cell sensitivity level and a cone cell sensitivity level. In some embodiments, the amount of illumination is in the range of approximately 10 cd / m 2 to approximately 50000 cd / m 2 such as from 100 cd / m 2 to approximately 50000 cd / m 2 , preferably from 10 cd / m 2 to 2000 cd / m 2 In some embodiments, the amount of illumination is in the range of approximately 0.1 cd / m 2 to approximately 10 cd / m 2 , such as from 0.5 cd / m 2 to 5 cd / m 2 For example, the amount of illumination can correspond to the amount of light between moonlight and indoor lighting. In some embodiments, the amount of illumination corresponds to mesopic vision.

[0095] In some embodiments, the microdisplay 12 can include a light source that emits polychromatic light composed 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 from 500 nm to 530 nm, more preferably from 500 nm to 510 nm.

[0096] In some embodiments, the polychromatic light source provides chromatic cues to the peripheral retina. The chromatic cues can include negative chromatic aberration. In some embodiments, the polychromatic light beam is focused in front of the retina, where the polychromatic light beam includes positive chromatic aberration before the image plane 35 or focal plane and negative chromatic aberration after the image plane 35 or focal plane, so as to illuminate the retina with negative chromatic aberration.

[0097] While the polychromatic illumination can be configured in many ways, in some embodiments, the polychromatic illumination includes red, blue, and green illumination, although other wavelengths of light can also be used.

[0098] In some embodiments, the projected images occur about 1.5 mm to about 2.5 mm in front of the peripheral retina, as they will be designed to be about 2.0 D to 4.0 D myopic, for example from 2.5 D to 3.5 D. In some embodiments, the projected images occur about 1.5 mm to about 2.5 mm in front of the peripheral retina, as they will be designed to be about 2.0 D to 7.0 D myopic, preferably 2.5 D to 5.5 D. Generally, 1 mm in front of the retina corresponds to about 2.5 D of myopia, for example about 2.7 D of myopia.

[0099] This method of peripheral stimulation of axial length changes through choroidal thickening or thinning can be based on repeated and confirmed observations of the effectiveness of applying local hyperopic or myopic defocus to stimulate axial length changes in the eye 11. The length and duration of the peripheral stimulation can be based on preclinical data available in animal models known to those of ordinary skill in the art. For example, the rate of change of axial length can be obtained based on repeated application of defocus stimulation, rather than a single duration period based on the equivalent duration of the applied defocus.

[0100] In some embodiments, the duration and distribution of the peripheral myopic defocus application depends on the individual physiology and shape of the retina. In some embodiments, the contact lens 10 includes a programmable processor, such as a microcontroller unit (MCU) or an application-specific integrated circuit (ASIC), to control the operation of the microdisplay 12. The contact lens 10 can include a real-time clock to adjust the treatment duration and period by a caregiver, and can provide the treatment duration and period throughout the treatment. In some embodiments, the caregiver tests whether the night stimulation (a continuous or repeated sequence of short pulses) is effective for a particular individual.

[0101] Glasses for retinal stimulation

[0102] Figure 1A and Figure 1B Eyeglasses 70 for treating refractive errors of the eye, suitable for combination according to this disclosure, are depicted. Although eyeglasses are referenced, light sources can be provided on any visual device described herein, such as augmented reality (“AR”) devices, to treat refractive errors of the eye and reduce or reverse myopia progression. Multiple light sources are arranged for treating myopia. For example, these multiple light sources can include any suitable light source as described herein, such as a microdisplay or projection unit. In some embodiments, as described herein, the light sources are configured to provide illumination at the peripheral retina to promote changes in the choroid and scleral tissues corresponding to different changes in axial length. Lenses can include optical zones having optical properties (e.g., refractive properties) configured to treat refractive errors of the eye and reduce or reverse myopia progression. This refractive treatment can be combined with retinal stimulation as described herein.

[0103] Glasses 70 may include one or more components of commercially available augmented reality glasses, such as the ORA-2 commercially available from Optinvent (which is showcased on Optinvent.com on the Internet). Glasses 70 may include one or more displays 72 for retinal stimulation. Near-eye displays 72 may be mounted to lenses 74. Lenses 74 may be spectacle lenses supported by spectacle frames 76. Lenses 74 may be corrective or uncorrective lenses. Lenses 74 may be plano lenses, spherical corrective lenses, astigmatic corrective lenses, or prism corrective lenses. In some embodiments, the near-eye displays are positioned away from the optical zone to provide clear central vision, such as the real world in a field of view ranging from + / -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 object of the patient's attention through lens 74 to the fovea of ​​the eye. In some embodiments, glasses 70 includes an eye tracker adapted for integration according to this disclosure. The near-eye display 72 can be programmed to selectively activate pixels 94 to provide peripheral stimulation to the retina, as described herein. In some embodiments, a plastic substrate layer carrying microlenses is attached to the microdisplay to generate a desired level of defocus and stimulation at the retina. The selectively activated pixels can be arranged to provide an appropriate degree of eccentricity relative to the patient's line of sight to provide peripheral retinal stimulation as described herein.

[0104] In some embodiments, the near-eye display 72 includes a combination of a microdisplay and micro-optics. The microdisplay can be placed close enough to the eye that the eye does not accommodate to focus the light rays emanating from the near-eye display, even though the human eye can use the full range of natural accommodation. In some embodiments, the micro-optics are configured to collect, substantially collimate, and focus the light rays emanating from the microdisplay. In some embodiments, the micro-optics are configured to form an image of the display in front of or behind the retina, as described herein. In some embodiments, the near-eye display is at a distance from the entrance pupil of the eye that is in any suitable range, such as a range from about 10 mm to about 30 mm, or a range from about 18 mm to 25 mm, for example at a distance of about 15 mm. The microdisplay can be placed on a transparent substrate, such as on 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 74, then the focal point of the microdisplay can be affected by the refractive correction on the back surface of the lens 74.

[0105] In some embodiments, the focal points of the pixels in the microdisplay can vary based on their position on the lens 74 and the refractive correction provided by the lens in that area. In some embodiments, the focal points of the pixels can be fixed. In some embodiments, the focal points of the pixels can vary based on the sensed position of the cornea to account for the refraction of the cornea and lens of the eye. In some embodiments, the pixels are defocused to produce a defocused spot on the retina that is about 1 mm in diameter.

[0106] The light emitted by the pixels 94 in the microdisplay of the near-eye display can be one or more of substantially collimated or focused light before being directed to the pupil of the eye. In some embodiments, a microlens array is aligned with the pixels of the near-eye display such that the light rays from the near-eye display can enter the pupil and form an image in front of or behind the retina. In some embodiments, the width of the near-eye display corresponds to the field of view of the patient. In some embodiments, the range of the near-eye display can be substantially similar to the range of the lens 74 of the eyeglasses 70. In some embodiments, the near-eye display can be curved such that the light rays from the pixels can be normal with respect to the pupil plane across the entire width of the display. In some embodiments, a prism tilt is provided to the lenses in the microlens array in order to compensate for the tilt of the plane of the microdisplay away from the pupil plane.

[0107] Work related to the present disclosure indicates that when myopic defocus retinal stimuli are applied in the periphery, it can be more effective in preventing myopia progression 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 a suitable time for treatment for two years or more to maintain the wearer's emmetropia or to guide the eye toward emmetropia growth, for example, if the wearer's eye has a tendency to shift to a myopic optical configuration. In some embodiments, the vision correction device is configured to be worn for a relatively long period of time, for example, for several hours a day over a period of 1 month and up to 2 years, depending on, for example, the rate of myopia reversal. The refractive prescription of the central optic zone can change in response to treatment. For example, if the myopia degree decreases, the myopic correction of the central optic can be reduced. The refractive power of the treated eye can be measured at any suitable period of time, such as monthly, and the prescription of the central optic zone is changed as appropriate.

[0108] In some embodiments, the device provides unimpaired central vision so that the wearer's quality of life and visual quality are not adversely affected. In some embodiments, the central vision includes a field of view of + / - 12.5 degrees covering the macula, while the foveal vision for fixation has a field of view of + / - 2.0 degrees. In some embodiments, the central vision includes a field of view of + / - 4.5 degrees covering the macula, while the foveal vision for fixation has a field of view of + / - 2.0 degrees. In some embodiments, the defocused images are projected toward the periphery of the retina at an outer portion of the retina, for example, in a range of 15 degrees to 40 degrees eccentric to the fovea, and can be in a range from 20 degrees to 30 degrees. In some embodiments, the microdisplay 72 does not obstruct the central vision field of view. In some embodiments, the pixels 94 do not obstruct the central vision field of view.

[0109] Alternatively or in combination with the eccentricity of the myopic defocus images, the device can be configured to illuminate an image or an appropriately sized area of the image footprint on the retinal cup. Work related to the present disclosure indicates that it can be helpful to illuminate at least a portion of each of the four quadrants of the retina. In some embodiments, each image on the retinal quadrant occupies an arc of approximately 45 degrees circumferentially. In some embodiments, each image on the retinal quadrant occupies an arc of approximately 30 degrees circumferentially. Illumination in the appropriate amount at the appropriate location can provide stimulation to the eye that causes choroid and ultimately sclera remodeling and a shortening of the axial length of the eye and thereby reduces myopia.

[0110] The microdisplay and optics can be configured in many ways to provide appropriate stimulation to the peripheral regions of the retina that are oriented toward the periphery. In some embodiments, the microdisplay and optics are configured to project light onto a region of the retina far enough from the fovea that the illumination remains substantially fixed even in the presence of eye movements. In some embodiments, the point of regard is monitored and (e.g., by using a processor to compute) a desired location of the pixel to be activated on the microdisplay is determined, thereby projecting the image to a desired location on the retina, to allow for sustained stimulation at the same retinal location. In some embodiments, the point of regard is computed by monitoring horizontal, vertical, and torsional displacements of the eye relative to a primary position.

[0111] The point of regard can be determined in many ways, for example by an eye position sensor such as a magnetic sensor or an optical sensor. In some embodiments, search coils embedded in the eyeglass frame are used to track eye movements. The coils embedded in 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 implanted in the eye, a magnetic material on a contact lens, or a magnetic material implanted in the eye. In some embodiments, the sensor includes an optical sensor such as a position sensitive 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 configured to measure the position of one or more of a light source, a pupil, a limbus, or a corneal reflection from the limbus. The eyeglass frame can support additional light sources to illuminate the eye, for example to generate a corneal reflection. Data from the sensor can provide the position of the coaxial visual corneal light reflection (“CSCLR”), thereby providing the direction of the visual axis and the location of the fovea. The point of regard, the visual axis, the optical axis, the nodal point of the eye, and the CSCLR are described in the article “Ocular axes and Angels: time for better understanding,” Srinivasan, S., in J CATARACT REFRACT SURG, vol. 42, March 2016.

[0112] In some embodiments, the near-eye display includes a transparent flexible substrate that matches the curvature of the eyeglasses worn by the user. The near-eye display can be mounted on the outside of the optics and the frame of the eyeglasses. The frame and temples can be hollowed out or shaped appropriately to accommodate electronics, including electronic drivers for the display, a rechargeable battery to provide power to the system, memory to store algorithms that control the operation of the near-eye display. The device can be recharged in many ways, for example by using a micro-USB port, or by using a recharging module for wireless recharging.

[0113] In some embodiments, a processor using eye position sensors can be configured to adjust optics, such as pixels in a microdisplay, to reduce movement of a stimulated location of the retina in response to eye movements. In some embodiments, a target location of a peripheral image is calculated from a location of the fovea based on information from eye position sensors, and real-time ray tracing calculations provide locations of pixels in the microdisplay to be activated. The time to selectively switch to a second plurality of pixels in response to eye movements can be less than 100 milliseconds, for example less than 20 milliseconds.

[0114] In some embodiments, the locations of pixels in the microdisplay to be activated to form an external image toward the periphery of the retina are referenced to an optical center of the eyeglass optical piece, as this is the point of regard when the primary gaze. In some embodiments, the location of the point of regard is calculated by taking into account eye movements relative to the position of the eye when the primary gaze, and the location of pixels to be activated is calculated with reference to the new point of regard. For example, Figure 1A Active pixels 94 are shown when the patient is looking straight ahead and directly forward (i.e., the so-called primary gaze). Figure 1B Active pixels 94 are shown when the patient is looking up and to the left. In this case, the shape of the array of pixels can be the same but translated up and to the left, or the shape of the array can change. In some embodiments, the plurality of light sources, e.g., active pixels 94, are configured to change to maintain alignment of the optical axis of the eye. This alignment can be provided by processor instructions configured to selectively activate pixels according to eye movements and the optical axis of the eye.

[0115] In some embodiments, the near-eye display module is mounted on the outside of the eyeglass lens. Alternatively, the near-eye display can be mounted on the inside of the eyeglass lens. In some embodiments, the device is binocular and includes a microdisplay and optics for each eye of the wearer. The microdisplay can be optically coupled with one or more micro-optical components designed to substantially collimate and render convergent the illumination generated by the pixels of the microdisplay before it enters the pupil.

[0116] In some embodiments, the display 72, e.g., display module, is mounted on the outside of the eyeglass lens and aligned with the eyeglass lens optical piece so that the near-eye display can provide a field of view of + / - 40 degrees or more so that the microdisplay can continue to provide peripheral retinal stimulation for a normal range of eye movements, which is typically + / - 15 degrees laterally, such as + / - 5 degrees laterally, and +10 to -20 degrees vertically, such as + / - 7 degrees vertically, or + / - 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 optical piece and provides refractive correction for the wearer.

[0117] In embodiments, the refractive correction includes one or more of a spherical correction or a correction for astigmatism. In some embodiments, the correction includes a prismatic correction for correction of strabismus and a correction for hyperopia, such correction can vary across the optical piece of the eyeglass lens, such as a progressive addition lens (“PAL”). In some embodiments, the micro-optics of the near-eye display are configured to provide the myopic defocus required to generate peripheral retinal stimulation (e.g., by forming an image in front of the retina that stimulates the peripheral regions of the retina) to prevent myopia development, as described herein.

[0118] In some embodiments, the optical system is configured to form an image in front of the retina and it includes one or more of a single micro-lens (lenslet), a plurality of micro-lenses (lenslet array), a compound lens (such as a Gabor lens), a micro-prism, or a micro-mirror, or a combination thereof. In some embodiments, the light barrier and the micro-mirror are arranged to ensure that the amount of light that is not captured by the micro-optics is significantly reduced, e.g., minimized, in order to reduce stray light and light escaping from the front side of the display.

[0119] In some embodiments, a pixel fill factor of less than 10% (0.1) is sparse enough 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 be in the range from 0.05 to 0.20. For example, a pixel array with a pixel size of 5 microns and a pixel pitch of 20 microns results in a fill factor of 0.06. A low fill factor can also reduce the complexity of the manufacturing process and reduce the cost of such micro-optical displays.

[0120] In some embodiments, the micro-optics array is designed to be optically aligned with the display so that light from a single or multiple pixels 94 can be collected, collimated, and focused to be directed to the pupil of the wearer at primary gaze. The density of these micro-optical elements can control the overall visibility of the near-eye display. In some embodiments, the micro-optics have a low fill factor (preferably equal to or less than 0.1) so that the total light transmission through the near-eye display is acceptable to the wearer and allows the patient to see objects.

[0121] In some embodiments, the device includes a switchable micro-optics array that can be switched between a flat (no optical power) state and an activated state by electro-optical means, for example, switched with liquid crystals or LC-based materials that can switch, for example, from one refractive index to another, or from one polarization to another. In some embodiments, when the micro-optics array is not activated, they do not scatter light or distort the real-world image.

[0122] In some embodiments, the position of the pixels in the microdisplay to be activated to form the outer image towards the periphery of the retina is referenced to the optical center of the eyeglass optics, as this is the point of regard at primary gaze. In some embodiments, the position of the point of regard is calculated by taking into account eye movements relative to the position of the eye at primary gaze, and the position of the pixels to be activated is calculated with reference to the new point of regard.

[0123] In some embodiments, a plurality of 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 provide the focal length of the image delivery system, the image magnification of the image projected on the retina, and the blur caused by diffraction, as measured by the Airy disc diameter of the optical delivery system.

[0124] According to some embodiments, the technical specifications are given in Table 1.

[0125] Table 1. Optical specifications for an augmented reality near-eye display for preventing myopia progression

[0126]

[0127] The optical resolution or quality of the peripheral projected image is related to three factors: the depth of focus, the image magnification, and the Airy disc diameter. The depth of focus of a near-eye display depends on the focal length and the aperture of the near-eye display and the image magnification (Equation 1).

[0128] Depth of focus = 2N*c*(1+m) (Equation 1)

[0129] When N is the f-number (f / D, where f is the focal length and D is the diameter), c is the minimum circle of confusion, and m is the image magnification.

[0130] In a typical eye, a -1.0 D myopic defocus causes the image at the best focus to move forward by about 0.35 mm.

[0131] The resolution of the retina decreases with the degree of eccentricity, so when the degree of eccentricity is in the range of 20-40 degrees, it is desirable that the resolution of the retina in the range of eccentricity drops to 20 line pairs / mm. It has been found that even at these eccentricities, the retina is able to detect the presence of stimuli at higher spatial frequency levels. Therefore, in some embodiments, the array of micro-optics designed to form and project the peripheral image is corrected for optical aberrations and is able to form an image with an OTF modulus equal to or better than 0.3 at a spatial frequency of 50 lp / mm or more.

[0132] Work related to the present disclosure indicates that the retina perceives changes in image blur caused by higher order aberrations present in defocused images (in addition to spherical defocus), including longitudinal chromatic aberration (LCA) that is sensitive to the sign of defocus, higher order spherical aberration, astigmatism, etc. Based on the teachings provided herein, one of ordinary skill in the art can conduct experiments to determine whether the retina can distinguish between myopic and hyperopic blur when the depth of focus of the device is greater than or nearly equal to the magnitude of defocus. A device as described herein can be suitably configured to provide, for example, an appropriate amount of defocus at an appropriate location.

[0133] The device can be configured to provide an appropriate image magnification, diffraction, which limits image resolution and depth of focus, which is related to the magnitude of myopic defocus applied, and the rate of change of image blur or image sharpness gradient as a function of the magnitude of defocus. The human eye can have a lower blur perception threshold. Since the strength of the growth signal to the retina and choroid depends on the magnitude of myopic defocus perceived from the image defocus, the extent of defocus and blur perception can be considered in estimating the expected strength of the growth signal generated by a particular optical configuration with respect to the magnitude of myopic defocus applied to the retinal image by a near-eye display.

[0134] In some embodiments, the near-eye display is configured to provide a clear, substantially undistorted field of view of the foveal and macular image for comfortable vision. In some embodiments, the field of view of the central image is at least + / - 12 degrees or at least + / - 5 degrees, and can 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 using a substantially transparent near-eye display, and can be provided by reducing the fill factor of the light emitting pixels in the microdisplay. In some embodiments, a fill factor of less than 10% (0.1) is sparse enough to provide a clear view of the foveal and macular image. In some embodiments, the fill factor is in the range of 0.01 to 0.3, and can be in the range of 0.05 to 0.20. For example, a pixel array with a pixel size of 5 microns and a pixel pitch of 20 microns would result in a fill factor of 0.06. The low fill factor can also reduce the complexity of the manufacturing process and reduce the cost of such micro-optical displays.

[0135] In some embodiments, the array of micro-optics is designed to be optically aligned with the display such that light from a single or multiple pixels can be collected, collimated, and focused to be directed toward the pupil of the wearer at the primary gaze. The packing density of these micro-optical elements can control the overall visibility of the near-eye display. In some embodiments, the micro-optics have a low fill factor (preferably equal to or less than 0.1) such that the overall light transmission through the near-eye display is acceptable to the wearer.

[0136] In some embodiments, the device includes a switchable micro-optics array that can be switched between a flat (no optical power) state and an active state by electro-optical components, for example switched with liquid crystals or LC-based materials that can switch, for example, from one refractive index to another, or from one polarization to another. In some embodiments, when the micro-optics array is not activated, the micro-optics array does not scatter light or distort the real-world image.

[0137] Retinal stimulation light source and circuit

[0138] Figure 2A An OLED microdisplay 12 mounted on the inner surface of a lens such as a soft contact lens 10 is shown, optically coupled with a microlens array for projecting an image with a de- focus value on the wearer's retinal periphery.

[0139] Figure 2B A lens such as a soft contact lens 10 is shown that includes a plurality of light sources and optics and associated circuitry, according to some embodiments.

[0140] Although Figure 2A And Figure 2B Reference is made to a contact lens, but the lens can include a lens of one or more of a projector, an ophthalmic device, a TV screen, a computer screen, a hand-held device such as a smartphone, a wearable device such as glasses, a near-eye display, a head-mounted display, goggles, a contact lens, a corneal onlay, a corneal inlay, a corneal prosthesis, or an intraocular lens.

[0141] 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 to focus light in front of the retina, as described herein. Each optic can 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 waveguide. The contact lens 10 can include a battery 20 and a sensor 22. The contact lens 10 can include a flexible printed circuit board (PCB) 24, and a processor can be mounted on the PCB 24. The processor can be mounted on the PCB 24 and coupled to the sensor 22 and the plurality of light sources 30. The soft contact lens 10 can also include wireless communication circuitry and an antenna for inductive charging of the contact lens 10. Although reference is made to a battery 20, the contact lens 10 can include any suitable energy storage device. The soft contact lens 10 can include a lens body composed of any suitable material such as a hydrogel. The hydrogel can encapsulate the components of the soft contact lens 10.

[0142] The processor can be configured with instructions to illuminate the retina with multiple light sources 30. The processor can be programmed in a variety of ways, for example, by instructions received with the wireless communication circuit. The processor can receive instructions for the user's mobile device.

[0143] The sensor 22 can be coupled to the processor to allow the user to control the contact lens 10. For example, the sensor 22 can be configured to respond to pressure, such as pressure from the eyelid. The processor can be coupled to the sensor 22 to detect user commands.

[0144] The electronic control system can include a processor such as an ASIC or microcontroller, a rechargeable lithium-ion solid-state battery, a voltage ramp module (e.g., a buck-boost converter), a flash memory and EEPROM, an RFID module for providing wireless recharging, or preferably an antenna disposed radially near the edge of the contact lens 10, and any combination thereof. The contact lens 10 can include a biocompatible material such as a soft hydrogel or a silicone hydrogel material, and can include any material composition that has been shown to be compatible with the continuous wear of the contact lens 10 on the eye 11.

[0145] Figure 2C A mechanical integration of the functions of the components of the lens of the contact lens 10 is shown, such as Figure 2B The components can be supported with the PCB 24. For example, a power source such as the battery 20 can be mounted on the PCB 24 and coupled to other components to provide the power supply function 21. The sensor 22 can be configured to provide the activation function 23. The sensor 22 can be coupled to a processor mounted on the PCB 24 to provide the control function 25 of the contact lens 10. The control function 25 can include the light intensity setting 27 and the light switch 29. The processor can be configured to detect a signal from the sensor 22 that corresponds to an increase in intensity, a decrease in intensity, or an on / off signal from the sensor 22, for example, a coded sequence of signals from the sensor 22. The processor is coupled to the light projection unit 18, which can include the light source 30 and the optics 32 to provide the projection function 31. For example, the processor can be coupled to multiple light sources 30 to control each light source 30 in response to user input to the sensor 22.

[0146] Optical configuration with projection optics

[0147] In some embodiments, the optical configuration 32 includes multiple mirrors configured to collect light emitted by the microdisplay 12 and then direct the light beams to the pupil of the eye 11 so as to form an eccentric retinal image, as shown in Figure 3 and Figure 4 The mirrors can collimate the light beams, or direct the light beams toward the retina 33 with an appropriate degree of divergence so as to focus the light beams onto the retina 33.

[0148] Although Figure 3 And Figure 4 The optical configurations shown refer to lenses such as contact lenses, but similar optical configurations can be used with lenses of one or more of a projector, an ophthalmic device, a TV screen, a computer screen, a hand-held device such as a smartphone, a wearable device such as glasses, a near-eye display, a head-mounted display, goggles, a contact lens, a corneal onlay, a corneal inlay, a corneal prosthesis, or an intraocular lens. Also, although reference is made to myopic defocus, the defocus can include hyperopic defocus, or an image focused onto the retina, for example.

[0149] The specifications of the example optical configurations are shown in Table 2.

[0150] Table 2. Figure 3 The basic optical parameters of the optical configurations shown

[0151]

[0152] Figure 3 A comparison of the simulated image size to the retinal resolution at 27 degrees of decentration for the optical configurations shown indicates that the peripheral retina 33 will be able to perceive the image at that decentration.

[0153] In some embodiments, the three performance attributes of the optical configurations include one or more of the following:

[0154] 1. Image magnification, which controls image resolution;

[0155] 2. Depth of focus, which is controlled by the optical path length of the optical configuration; and

[0156] 3. Diffraction, which is measured in terms of the Airy disk.

[0157] Figure 3 The mirror assemblies shown achieve a depth of focus of less than 1D, such that a defocus of 2.0D to 4.0D or 2.0D to 7.0D applied can be clearly perceived by the peripheral retina 33 at the specified decentration (20 degrees to 30 degrees or 10 degrees to 40 degrees).

[0158] In some embodiments, the spot size of the image focused in front of the retina 33 includes a resolution that is finer than the resolution of the retina 33. The retinal resolution generally decreases as a function of decentration. For example, at 0 degrees of decentration, the retinal resolution is about 10 microns. At 5 degrees of decentration, the retinal resolution is about 30 microns. At 20 degrees of decentration, the resolution is about 100 microns, and at 30 degrees of decentration, the retinal resolution is about 150 microns.

[0159] Figure 5A And Figure 5BAn analysis of the retinal image quality generated by the optical configuration of Figure 3 is shown. The image formed by three of the four light sources 30 has been simulated. The temporal point has been omitted as it is symmetrical to the nasal point. The analysis shows that at an eccentricity of 27 degrees the image quality exceeds the resolving power of the retina 33. According to this embodiment, the modulation transfer function of the retinal image produced by the mirror assembly of Figure 3 is diffraction limited, which indicates that the aberrations of the deployed optical elements do not cause a significant deterioration of the image quality. Furthermore, the spatial resolution of the optics exceeds the resolution of the retina 33 at the preferred image location.

[0160] Figure 6 An analysis of the depth of focus of the optical configuration shown in Figure 3 is shown. Each millimeter of distance from the retina 33 represents a defocus of 2.7D. This analysis shows that the depth of focus is small enough so that the retina 33 can perceive a defocus of 0.5mm (1.35D) at the point of incidence of the image (27 degrees of eccentricity). The depth of focus depends on the effective path length of the stimulating light beam.

[0161] Figure 7 A plot of the MTF values versus defocus is shown, showing the depth of focus of the image created by each of the light sources (objects).

[0162] A second embodiment comprises optics 32 comprising converging or collimating lenses optically coupled with the light sources 30, as shown in Figure 8A and Figure 8B In this configuration, a lens 34, which can comprise a single lens, is used to collimate the light output from the stimulating source and direct the light to the cornea 37 through a lens such as a contact lens 10. Although reference is made to a contact lens, the lens 10 can comprise a lens of one or more of a projector, an ophthalmic device, a TV screen, a computer screen, a hand-held device such as a smartphone, a wearable device such as glasses, a near-eye display, a head-mounted display, goggles, a contact lens, a corneal onlay, a corneal inlay, a corneal prosthesis or an intraocular lens.

[0163] The effectiveness of the collimating lens 34 depends on its refractive index, and it should be high enough so as to create a significant refractive index difference between the lens material and the contact lens 10 material used as a substrate. In this example, the refractive index of the embedded lens 34 is assumed to be 2.02 (e.g. the refractive index of lanthanum fluoride-silica glass LaSF5), although other materials can be used.

[0164] Figure 8A and Figure 8B The optical performance of the embodiment of Figure 9 and Figure 10An image formed by three of the four light sources 30 has been simulated. The temporal point has been omitted as it is symmetrical to the nasal point. Each millimeter of distance from the retina 33 represents 2.7D of defocus. This analysis shows that the depth of focus is substantially higher than 1D, so at the point of incidence of the image (27 degrees of decentration), the retina 33 can not perceive the image blur caused by 0.5mm (1.35D) of defocus.

[0165] The analysis shows that at 27 degrees of decentration, the image quality exceeds the resolving power of the retina 33. In this case, the optical path length of the single lens design is much shorter, and therefore, the image magnification is significantly higher (110X, as opposed to 8X or 20X for the reflective design). The spatial frequency resolution at 50% contrast (OTF modulus) is lower, about 15 line pairs per millimeter (“lp / mm”), as compared to the reflective design, which is 50 lp / mm. For this embodiment, the depth of focus has been estimated, again using the Liou Brennan eye model to simulate the eye optics, including eye aberrations, as Figure 10 shown. The depth of focus is greater than 1.0D, which indicates that the change in image resolution as a function of defocus can not be easily perceived by the peripheral retina 33, especially because the resolving power of the retina 33 at this decentration (20 to 30 degrees or 10 to 30 degrees) is relatively poor, primarily from the rod cells, as described herein.

[0166] A third embodiment includes a light pipe 36 to increase the optical path length, as Figure 11A and Figure 11B shown. The light pipe 36 can provide an increased optical path length to reduce the image magnification and to reduce the retinal image size. However, the depth of focus is relatively large, and the resolution is relatively coarse (15 lp / mm at 50% MTF).

[0167] Although reference is made to a light pipe 36 on the cornea 37, as would occur with the use of a contact lens, the lens in combination with the light pipe 36 can include a lens of one or more of a projector, an ophthalmic device, a TV screen, a computer screen, a hand-held device such as a smartphone, a wearable device such as glasses, a near-eye display, a head-mounted display, goggles, a contact lens, a corneal onlay, a corneal inlay, a corneal prosthesis, or an intraocular lens.

[0168] Many other optical configurations can be used, including using a microlens array with a point source, using diffractive optics in order to use a thinner lens, using a single point source and an optical processing unit to generate multiple retinal images. In all cases, the three characteristics listed above can be used as metrics in order to evaluate the suitability of a particular design.

[0169] Each of the embodiments 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 that many such combinations are within the scope of the present disclosure.

[0170] Example lens embodiments

[0171] The methods and apparatus disclosed herein 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-optic contact lenses, contact lenses with flexible conductors, autonomous eye tracking contact lenses, electrochromic contact lenses, dynamic diffractive liquid crystal lenses, auto-adjusting lenses, image display lenses with programmable phase maps, lenses with tear activated microbatteries, tear film sensing contact lenses, lenses with multicolor LED arrays, contact lenses using capacitive sensing, lenses for detecting coverage of ophthalmic devices by eyelids, lenses with active adjustment, lenses with electrochemical sensors, lenses with enzymes and sensors, lenses including dynamic field of view adjustment, lenses for measuring pyruvate, lenses for measuring urea, lenses for measuring glucose, lenses with tear conductivity sensors, lenses with near-eye displays with phase maps, or lenses with electrochemical sensor chips.

[0172] A lens, such as soft contact lens 10, is shown in Figure 12 Although reference is made to a contact lens, lens 10 can include a lens of one or more of a projector, an ophthalmic device, a TV screen, a computer screen, a handheld device such as a smartphone, a wearable device such as glasses, a near-eye display, a head-mounted display, goggles, a contact lens, a corneal onlay, a corneal inlay, a corneal prosthesis, or an intraocular lens.

[0173] The contact lens 10 includes a base or carrier contact lens, which includes embedded electronics and optics. The base soft contact lens 10 is made of a biocompatible material such as a hydrogel or silicone hydrogel polymer, designed for continuous wear. In some embodiments, the contact lens 10 has a central optical zone 14 with a diameter ranging from 6 mm to 9 mm, for example, from 7.0 mm to 8.0 mm. The central optical zone 14 is defined by an outer annular zone (such as a peripheral zone 16 with a width ranging from 2.5 mm to 3.0 mm). The outer annular zone is surrounded by an outermost edge zone 18 with a width ranging from 0.5 mm to 1.0 mm. The optical zone 14 is configured to provide refractive correction and may be, for example, spherical, curved, or multifocal in design. The outer annular zone surrounding the optical zone 14 is configured to fit the corneal curvature and may include a rotational stabilization zone for translational and rotational stabilization while allowing the contact lens 10 to move across the eye 11 with blinking. The edge region 18 may include a thickness ranging from 0.05 mm to 0.15 mm and may end in a wedge shape. The total 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.

[0174] like Figure 12 As shown, the embedded light source 30 and electronics are preferably located in the outer annular region of the contact lens 10. According to some embodiments, the central optical region 14 preferably does not contain electronics and the light source 30 to avoid impairing visual quality of the fovea or macula. In some embodiments, the peripheral region 18 does not include circuitry to maintain contact with the corneal surface and provide comfort.

[0175] Light sources can be arranged on contact lenses in a variety of ways. For example, light sources can be arranged in a substantially continuous ring around a central optical zone. In some embodiments, multiple light sources and multiple optical devices (e.g., lenses, mirrors, or light guides) are coupled together to form a continuous illumination ring.

[0176] Figure 12The contact lens 10 includes a body composed of a soft, biocompatible polymer with high oxygen permeability, in which a transparent film filled with all electronic and optical components is embedded. This transparent film may include a transparent printed circuit board (“PCB”) substrate. The PCB thickness may range from approximately 5 micrometers to 50 micrometers and may include multiple layers to utilize both surfaces of the PCB substrate for arranging electronic devices. The PCB substrate may be bent to conform to the geometry of the base contact lens 10; for example, the curvature of the PCB substrate may range from approximately 7.5 mm to approximately 10.0 mm, such as from approximately 8.0 mm to approximately 9.5 mm. The PCB substrate may be configured to have suitable oxygen permeability. In some embodiments, the PCB is perforated to improve the permeability of oxygen, tears, nutrients, and carbon dioxide through it. In some embodiments, the PCB has a low tensile modulus, for example, in the range of approximately 1 MPa to approximately 50 MPa, although a more rigid film may also be used, for example. In some embodiments, preferred materials for transparent flexible PCB substrates include polyimides cast from liquids or solutions, and when spin-cast onto a flat substrate, the polyimide may be in the form of polyamic acid, subsequently thermosetting to form a polyimide such as Kapton. TM .

[0177] Contact lens 10 may include Figure 12 One or more components are shown. The architecture of an electronic system, such as... Figure 12 As shown, the system includes multiple light sources 30 mounted on a bus, a microcontroller 38 including a power and data management system, onboard memory and an RFID module, sensors designed to detect physical or physiological triggers and emit signals to turn the light sources 30 on or off, an antenna 41 for wirelessly exchanging data (this antenna also functions as a wireless power receiver, operating on one or more frequency bands for transmitting data and power), and a rechargeable solid-state lithium-ion battery 20. In some embodiments, the microcontroller 38 includes an application-specific integrated circuit (“ASIC”). The multiple light sources 30 may include miniature light sources 30 as described herein.

[0178] The light source 30 can be positioned relative to the center along a circumference with a diameter ranging from 1.5 mm to 5.0 mm.

[0179] Figure 13 A ray-tracing analysis of an image formed by the light source 30 on an outer region of the retina 33 (such as the peripheral retina 33) is shown. In this simulation, the anterior chamber depth is assumed to be 4.1 mm, which is typically between 2.9 mm and 5.0 mm for human subjects, 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 from the center of the contact lens 10, leaving a clean central optical zone 14 with a diameter of 3.8 mm.

[0180] Referring again to Figure 12 and Figure 13 The combination of light source 30 and a lens, such as a microlens, can be used to direct light to the outer region of the retina 33. The microlens can be configured to collect light emitted by the light source 30. The collected light can be one or more of collimated or focused light and directed to the pupil of the eye 11. In some embodiments, the projection system includes a combination of micro light source 30 and imaging optics 32.

[0181] The light source 30 can include 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 can include one or more pixels arranged on a transparent or non-transparent substrate. For example, the light source 30 can include one or more display components, such as a passive matrix or an active matrix. In some embodiments, the size of a single pixel is in a range from 1 to 10 microns, for example, in a range from 2 to 5 microns. The luminance of each of the plurality of pixels when turned on can be greater than 500 nits (cd / m 2 ), greater than 5000 nits, or in a range from 10,000 to 25,000 nits.

[0182] The resolving power of the retina 33 is highest at the center, at the fovea. The angular resolution of a healthy young person is 0.6 minutes of arc, equivalent to 20 / 12 in Snellen terms. At 25 degrees of eccentricity, the resolution power typically decreases to 20 / 200 (10 minutes of arc). There are almost no cone cells at this eccentricity, and the number of rod cells is also greatly reduced.

[0183] In some embodiments, the image delivery system provides an image resolution that equals or exceeds the level of retinal image resolution. In some embodiments, if the projected image resolution exceeds the resolution capability of the retina 33 at the image location, no additional benefit can be expected. In some embodiments, the spot size of the image at the periphery of the retina is therefore 150 microns or less.

[0184] The wavelengths of light emitted by the light sources 30 can be configured in a variety of ways. In accordance with the present disclosure, the wavelengths of light emitted by the light sources 30 can be determined by clinical studies. In some embodiments, the wavelengths of the light sources 30 include light corresponding to the peak sensitivity of the retinal photoreceptors at the desired eccentricity, e.g., substantially matching the peak sensitivity. In some embodiments, the light is projected at an eccentricity of 10 to 30 degrees, such as 20 to 30 degrees, where the rod cells dominate, and the light from the light source includes wavelengths in the range from about 410 nm to 600 nm, such as 420 nm to 600 nm, e.g., from about 490 nm to 530 nm, for example, in the range from about 500 nm to 520 nm, e.g., from about 502 nm to 512 nm. In some of the wavelength simulations disclosed herein, 507 nm light was used as the input wavelength parameter. The optical designs disclosed herein are applicable to all wavelengths, even though the precise results of the optimization of the design parameters can change with wavelength due to the chromatic dispersion of the materials comprising the projection units.

[0185] Work related to the present disclosure indicates that in some embodiments below, two design constraints can influence the selection of the design input parameters. These are:

[0186] 1. The size of the projection units 18 such that they can be embedded into the contact lens 10 without making the lens thickness too high. 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.

[0187] 2. The optical path length between the micro light source 30 and the imaging system. This is related to the control of the image magnification and the magnitude of the 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 typically 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 (2.44Xl (in microns)xf / ≠) is no larger than the retinal resolution limit at the image location. For example, the minimum spot size at an eccentricity of 25 degrees is 150 microns, so the Airy disk diameter should not exceed 150 microns, and can also 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 for any wavelength.

[0188] In some embodiments, as described herein, the Airy disk size of the collection optics and the Airy disk size of the light source 30, as well as the size of the associated image, are related to the retinal image resolution. For example, at 30 degrees, 25 degrees, 20 degrees, 15 degrees, and 10 degrees, the Airy disk size can be no more than about 150 microns (“microns,”“um”), about 125 pm, about 100 pm, about 75 pm, and about 60 pm, respectively.

[0189] The imaging system can be configured in many ways, including but not limited to diffractive optical elements, Fresnel lenses, refractive optics, or reflective optics.

[0190] The following simulations provide optical results according to some embodiments disclosed herein.

[0191] Table 3. Input parameters for second optical simulation

[0192]

[0193]

[0194] In some embodiments, the area of the region covered by the overall image is preferably 5 degrees - 10 degrees by 30 degrees - 45 degrees of arc segment, or 150 degrees for each light source 2 - 450 degrees 2 , or an area of about 3.0 mm 2 - 6.0 mm 2 In some embodiments, four such light sources 30 at each quadrant of the contact lens 10 deliver four such peripheral images to the retina 33 for optimal neural stimulation. Figure 3 An embodiment according to a second simulation of the image delivery system is shown in FIG. 6. In this embodiment, a system of convex micro-mirrors 26 and concave micro-mirrors 28 is used to increase the optical path length, thereby increasing the image magnification of the peripheral retinal image. Figure 4 The optical path of the peripheral image through the eye 11 for the present embodiment is shown. An exemplary light source 30 can be defined as follows: assume the diameter of the light source 30 is 10 pm, and the thickness is 100 pm. Four object points 40 can be specified to simulate image quality, as shown in Figure 14 Referring to Figure 14 , the simulated light source 30 is shown as a dashed circle of 10 pm, and the simulated object points 40 include smaller circles and the center point of each smaller circle. Table 3 shows the input parameters for the simulation.

[0195] The output of the simulation is image magnification and size, image quality, and depth of focus. The same input parameters and output parameters are used to simulate all of the preferred embodiments. The image size for the first preferred embodiment was found to be 200 microns, and the image magnification was found to be 20X. The results of the simulation of image quality are shown in Figure 15 FIG. 6. All of the MTF plots are virtually identical. The MTF plots indicate that the resolution of the peripheral image is significantly better than the limit of retinal resolution at this decentration.

[0196] In a second simulation, the depth of focus of the peripheral image for a reflective optic was also simulated, and is shown in Figure 16 In some embodiments, the image is best formed at a distance of 2.0 mm in front of the retina 33, making it myopically defocused on the retina 33. In some embodiments, the blur caused by this myopic defocus overcomes the effect of the depth of focus, such that the retina 33 perceives the blurred image to be moving forward, thereby decreasing the axial length of the eye 11. In some embodiments, the neural stimulus is sufficient to decrease the axial growth of the eye 11.

[0197] Figure 17 The effect of the image blur caused by myopic defocus is shown in the form of a loss of contrast or the modulus of the simulated MTF plot shown in the second simulation at a particular spatial frequency (20 / 200 or 10 arcminutes). Figure 16 The increase in spot size shown is reflected in the loss of amplitude of the MTF plot, and is consistent with the loss of amplitude of the MTF plot as a function of the amplitude of myopic defocus. The second simulation indicates that the projection unit focal length is 0.85 mm, the image size is 200 microns, and the image magnification is 20X. The Airy disk diameter was calculated to be 8.9 microns, while the Raleigh criterion is 10.9 microns.

[0198] Referring again to Figure 8A and Figure 8B which show a lens for collecting light from the light source 30 and directing the light toward the retina 33, and the optical path along the eye 11, respectively. In some embodiments, the light source 30 faces a refractive lens that substantially collimates the light that is ultimately projected in front of the peripheral retina 33 to produce myopic defocus of the peripheral image. Although a refractive lens is referenced, other lenses can also be used, such as diffractive optics and gradient index (GRIN) lenses. Table 4 shows the design parameters for the refractive lens used in the third simulation of a peripheral image.

[0199] Table 4. Design input parameters for the third simulation

[0200] Lens parameters Values Source diameter 10 microns Wavelength for simulation 507 nm Optics diameter 292 microns Optics thickness 250 microns Refractive index of microlenses 2.2 Image position on retina 27 degrees eccentricity Projection optics thickness 350 microns Source distance from center of contact lens 1.75 mm Collimating lens design 14th order asphere

[0201] The results of these simulations show that the image size is 1100 microns and the image magnification is 110. Figure 18 The MTF plots for the four object points 40 shown in Figure 14 The MTF plots for the four object points 40 shown in Figure 19 The MTF plots show that the image resolution is adequate for an image with a decentration of 27 degrees. The optical design of the second preferred embodiment results in a larger depth of focus, as shown in Figure 19 This means that, according to the first and second simulations, in some embodiments, the effective image blur is much smaller for myopic defocus in the range of 2D to 5D relative to the catadioptric optical device. The increased depth of focus is reflected in Figure 20 The MTF plots for the four object points 40 shown in Figure 3 and Figure 4 The MTF plots for the four object points 40 shown in

[0202] The third optical simulation shows that a refractive optical device can successfully project a peripheral retinal image with acceptable image size, image magnification, and depth of focus. Although the image size, magnification, and depth of focus can be slightly larger than in the catadioptric configuration of the second simulation.

[0203] Although the MTF values at high spatial frequencies (50 lp / mm and above) are lower for this refractive optical design compared to the catadioptric design, the image quality at high spatial frequencies can be less relevant at the peripheral location of the retinal image due to the reduced acuity. The third simulation shows that the focal length of the projection unit is 0.15 mm, the image size is 1100 microns, and the image magnification is 110 times. The Airy disk diameter is calculated to be 36.7 microns, while the Rayleigh criterion is 44.8 microns.

[0204] Referring again to the Figure 11A and Figure 11B , a fourth simulation was performed on this configuration including the light guide, the mirror, and the lens. In this simulation embodiment, the focusing lens is located at the end of the light pipe (exit aperture). In some embodiments, the light pipe includes a curved lens surface at the end to focus the light. In this light guide embodiment, the projection optics include a light guide that includes a mirror and a lens.

[0205] In some embodiments, the light source 30 is placed in the outer portion of the contact lens 10, for example, near the periphery, and the light from the light source is directed to the mirror, which collects the light and deflects the light towards the eye 11 to generate an image with myopic defocus in front of the peripheral retina 33, as described herein. In some embodiments, the function of the light guide is to increase the length of the optical path, thereby reducing the image magnification and increasing the resolution of the image formed in front of the retina 33.

[0206] Table 5. Lens parameters used as input for the fourth simulation

[0207]

[0208]

[0209] Table 5 gives the characteristics of the projection system used in the fourth simulation of the peripheral retinal image quality formed by the light guide embodiment. The image magnification is 14 and the image size is 140 microns. These simulations show that the image magnification is acceptable, the depth of focus is not as large as for refractive optics, but larger than for reflective optics. The fourth simulation shows that the focal length of the projection unit is 1.21 mm, the image size is 140 microns, and the magnification is 14 times. The Airy disk diameter is calculated to be 34.8 microns, while the Rayleigh criterion is 42.6 microns.

[0210] The three results of the second, third, and fourth simulations for the three respective configurations are compared to each other in terms of their size, depth of focus, and beam diameter, the depth of focus being generated by each defining the sharpness gradient of the off-focus image as a function of the myopic defocus amplitude. The results show that the second simulation, including reflective optics, has the best sharpness gradient, while the embodiment including refractive optics has the smallest sharpness gradient, with the light guide-based projection unit providing a limited sharpness gradient, as shown in Figure 24 Each of these approaches can be configured to reduce axial length growth, in accordance with the teachings disclosed herein.

[0211] As shown in Table 6, the three embodiments also differ considerably in the diameter of the optics.

[0212] Table 6. Optics diameters used in the three simulations

[0213] Configuration Optics diameter Reflective optics 1.1 mm Refractive optics 0.3 mm Optical guide optics 0.4 mm

[0214] The reflective optics and the light source 30 can be configured in a variety of ways, and other simulations can be performed to determine an appropriate configuration in accordance with the teachings disclosed herein. For example, Figure 14 The sharpness of the central object point shown can be neglected as its contribution to the neural stimulation can be limited. Such simulations and optimization can allow to reduce the diameter of the projection unit and its thickness, which is helpful when the system is embedded in a contact lens 10 providing a high level of comfort to the wearer as described herein. The design input parameters for the fifth simulation are shown in Table 7.

[0215] Table 7. Input parameters for the fifth simulation

[0216] Lens parameters Values Source diameter 10 microns Wavelength 507 nm Reflective lens optics diameter 900 microns Source eccentricity from center of contact lens 1.85 mm Optics thickness 200 microns Projection cell thickness including source 200 microns Position of peripheral retinal image 27 degrees eccentricity from fovea Optics design Asphere 10th order, Zernike polynomial 4th order

[0217] The results show that the image magnification can be increased to 25, providing a 250 micron image size 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 fifth image simulations is shown in Figure 25 and Figure 26 The sharpness gradient, i.e. the change in image spot size or MTF at a single spatial frequency as a function of the defocus amplitude of a myopic eye, is still quite acceptable while providing a reduced projection system size.

[0218] 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 configuration, these computing device(s) can each include at least one memory device and at least one physical processor.

[0219] As used herein, the term "memory" or "memory device" 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 example, a memory device can store, load, and / or maintain one or more modules described herein. Examples of memory devices include, without limitation, Random Access Memory (RAM), Read Only Memory (ROM), flash memory, Hard Disk Drives (HDDs), Solid-State Drives (SSDs), optical disk drives, buffers, variants or combinations of one or more equivalents, or any other suitable storage memory.

[0220] Furthermore, as used herein, the term "processor" or "physical processor" generally refers to any type or form of hardware-implemented processing unit capable of interpreting and / or executing computer-readable instructions. In one example, a physical processor can access and / or modify one or more modules stored in a memory device described above. Examples of physical processors include, without limitation, microprocessors, microcontrollers, Central Processing Units (CPUs), Field-Programmable Gate Arrays (FPGAs) implementing softcore processors, Application-Specific Integrated Circuits (ASICs), portions of one or more equivalents, variants, or combinations thereof, or any other suitable physical processor.

[0221] Although illustrated as discrete elements, the method steps described and / or illustrated herein can represent portions of a single application. Furthermore, in some embodiments, one or more of these steps can represent or correspond to one or more software applications or programs, which, when executed by a computing device, can cause the computing device to perform one or more tasks, such as method steps.

[0222] Additionally, one or more devices described herein can transform data, physical devices, and / or representations of physical devices from one form to another. For example, one or more devices described herein can receive image data of a sample to be transformed, transform the image data, output the results of the transformation to determine a 3D process, use the results of the transformation to perform the 3D process, and store the results of the transformation to produce an output image of the sample. Additionally or alternatively, one or more modules described herein can transform a processor, volatile memory, non-volatile memory, and / or any other part of a computing device from one form of computing device to another form of computing device by executing on the computing device, storing data on the computing device, and / or otherwise interacting with the computing device.

[0223] As used herein, the term “computer-readable medium” generally refers to any form of device, carrier, or medium capable of storing or carrying computer-readable instructions. Examples of computer-readable media include, without limitation, 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.

[0224] Those of ordinary skill in the art will appreciate that any of the processes or methods disclosed herein can be modified. The process parameters and sequence, either illustrated or described, are given by way of example only and can be varied as desired. For example, while the acts described herein can be illustrated and / or described in a particular order, these acts can not be order dependent.

[0225] Various example methods described and / or illustrated herein can also omit one or more of the steps described or illustrated herein, or include additional steps in addition to the disclosed steps. Moreover, the steps of any of the methods disclosed herein can be combined with any one or more of the steps of any of the other methods disclosed herein.

[0226] Unless otherwise stated, the terms “connected to” and “coupled to” (and their derivatives), as used in the specification and in claims, are to be construed as permitting both direct and indirect (i.e. via another element or component) connection. In addition, the terms “a” or “an,” as used in the specification and in claims, are to be construed as meaning “at least one.” Finally, for ease of use, the terms “including” and “having” (and their derivatives), as used in the specification and in claims, are interchangeable with the term “comprising” and are intended to have the same meaning as the term “comprising.”

[0227] A processor as disclosed herein can be configured with instructions to perform any one or more steps of any method as disclosed herein.

[0228] It will be understood that, although the terms“first,”“second,”“third,” etc. can be used herein to describe various layers, elements, components, regions, or sections, these terms are not intended to suggest any particular event sequence or order, except where otherwise expressly provided. These terms are simply used to distinguish one layer, element, component, region, or section from another layer, element, component, region, or section. Thus, a first layer, a first element, a first component, a first region, or a first section discussed herein could be termed a second layer, a second element, a second component, a second region, or a second section without departing from the teachings of the present disclosure.

[0229] As used herein, the term“or” is used inclusively to refer to items in the alternative and in combination.

[0230] Each embodiment disclosed herein can be combined with any one or more of the other embodiments disclosed herein, and a person of ordinary skill in the art will recognize many such combinations are within the scope of the present disclosure.

[0231] The present disclosure includes the following clauses.

[0232] Clause 1. An apparatus for providing stimulation to a retina of an eye, comprising:

[0233] one or more optical devices to project one or more images onto the retina outside the fovea to facilitate one or more of a change in axial length of the eye or a change in choroidal thickness of the eye.

[0234] Clause 2. The apparatus of clause 1, wherein the one or more images comprise one or more of a still image or a dynamic image.

[0235] Clause 3. The apparatus of clause 2, wherein the image comprises a dynamic image with a refresh rate in a range from 1 Hz to 200 Hz.

[0236] Clause 4. The apparatus of clause 1, wherein the one or more images comprise one or more of a monochromatic light or a polychromatic light comprising a wavelength in a range from 400 nm to 800 nm.

[0237] Clause 5. The apparatus of clause 1, wherein the image has information or content in a spatial frequency range from 1 cycle per degree to 60 cycles per degree, and optionally, the spatial frequency range is from 1 cycle per degree to 10 cycles per degree.

[0238] Clause 6. The device of clause 1, wherein the image comprises a contrast ratio in a range from 99.9% to 2.5%.

[0239] Clause 7. The device of clause 1, wherein the image comprises a decentration in a range from 5 degrees to 40 degrees relative to the fovea.

[0240] Clause 8. The device of clause 7, wherein the image illuminates the retina in the range in a pattern that extends substantially continuously 360 degrees around the fovea.

[0241] Clause 9. The device of clause 7, wherein the image illuminates a portion of the retina in the range.

[0242] Clause 10. The device of clause 1, further comprising circuitry to stimulate the retina using one or more images using temporal illumination, the temporal illumination comprising one or more of continuous illumination, discontinuous illumination, periodic illumination, or aperiodic illumination.

[0243] Clause 11. The device of clause 10, wherein the temporal illumination comprises periodic illumination having a duration in a range from 1 second to 24 hours.

[0244] Clause 12. The device of clause 10, wherein the temporal illumination comprises discontinuous illumination having a duration in a range from 1 second to 24 hours.

[0245] Clause 13. The device of clause 10, wherein the circuitry is configured to illuminate the retina when the subject is in one or more states of wakefulness, sleep, or somnolence.

[0246] Clause 14. The device of clause 1, further comprising circuitry to stimulate the retina using one or more images having a spatial illumination pattern, the spatial illumination pattern comprising one or more of a continuous spatial illumination pattern, a discontinuous spatial illumination pattern, a periodic illumination pattern, or an aperiodic spatial illumination pattern.

[0247] Clause 15. The device of clause 1, wherein the one or more images comprise a luminance in a range from 1 Troland to 1000 Troland.

[0248] Clause 16. The device of clause 1, wherein the one or more optics are configured to project the one or more images having an illuminance in a range from 100 nits to 50,000 nits or in a range from 1 nit to 10,000 nits.

[0249] Clause 17. The device according to clause 1, wherein the one or more images correct for refractive error of the eye.

[0250] Clause 18. The device according to clause 1, wherein the one or more images are defocused relative to one or more locations of the retina at which the one or more images illuminate the retina.

[0251] Clause 19. The device according to clause 18, wherein the one or more images are myopically defocused in a range from 2.0D to 7.0D and optionally in a range from 2.0D to 5.0D.

[0252] Clause 20. The device according to clause 18, wherein the one or more images are hyperopically defocused in a range from 2.0D to 7.0D and optionally in a range from 2.0D to 5.0D.

[0253] Clause 21. The device according to clause 1, wherein the one or more optics comprise components of a light projection system.

[0254] Clause 22. The device according to clause 21, wherein the light projection system comprises components of one or more of a projector, an ophthalmic device, a TV screen, a computer screen, a handheld device, a mobile computing device, a tablet computing device, a smartphone, a wearable device, a spectacle lens, a near-eye display, a head-mounted display, eyewear, contact lenses, an implantable device, a corneal on-lay, a corneal inlay, a corneal prosthesis, or an intraocular lens.

[0255] Clause 23. The device according to clause 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 device, a mobile computing device, a tablet computing device, a smartphone, a wearable device, a spectacle frame, a spectacle lens, a near-eye display, a head-mounted display, eyewear, contact lenses, an implantable device, a corneal on-lay, a corneal inlay, a corneal prosthesis, or an intraocular lens.

[0256] Clause 24. The device according to clause 1, comprising: a plurality of light sources; wherein the one or more optics comprise a plurality of projection optics coupled to the plurality of light sources to project a plurality of images in front of the retina.

[0257] Clause 25. The device according to clause 24, wherein the plurality of projection optics are arranged to project a plurality of images of the plurality of light sources to a plurality of peripheral regions of the eye retina with a degree of eccentricity relative to the fovea of the eye in a range from 5 degrees to 30 degrees and optionally in a range from 15 degrees to 30 degrees.

[0258] Clause 26. The device according to Clause 24, wherein each of the plurality of projection optics is arranged to project an image that is myopically defocused relative to the retinal surface, wherein the amount of defocus is in a range from 2.0D to 7.0D, and optionally in a range from 2.0D to 5.0D.

[0259] Clause 27. The device according to Clause 24, wherein each of the plurality of projection optics is located from 1.5mm to 5.0mm from the center of the contact lens, and optionally wherein the plurality of projection optics are positioned along a circumference of a circle.

[0260] Clause 28. The device according to Clause 24, wherein the plurality of projection optics comprises a plurality of imaging optics optically coupled to the plurality of light sources to project the plurality of images in front of the retinal surface.

[0261] Clause 29. The device according to Clause 28, wherein each of the plurality of light sources has a maximum span of no more than 26 microns, and optionally no more than 10 microns, and optionally wherein the maximum span comprises a diameter.

[0262] Clause 30. The device according to Clause 28, wherein each of the plurality of projection optics comprises one or more of a mirror, a lens, or a light guide.

[0263] Clause 31. The device according to Clause 30, wherein each of the plurality of imaging optics comprises one or more of a diffractive element, a Fresnel lens, or a compound Gabor lens.

[0264] Clause 32. The device according to Clause 30, wherein each of the plurality of imaging optics has a maximum span in a range from 200 microns to 1.5mm, and optionally wherein the maximum span comprises a diameter.

[0265] Clause 33. The device according to Clause 30, wherein each of the plurality of imaging optics is aspherical and corrected for image aberrations.

[0266] Clause 34. The device according to Clause 30, wherein each of the plurality of imaging optics comprises a combination of a convex mirror and a concave mirror.

[0267] Clause 35. The device according to Clause 33, wherein the each of the plurality of imaging optics forms an image in front of an outer portion of the retina with a decentration in a range from 1 degree to 30 degrees from the fovea, optionally in a range from 10 degrees to 30 degrees from the fovea, optionally in a range from 15 degrees to 30 degrees, and further optionally in a range from 25 degrees to 30 degrees.

[0268] Clause 36. The apparatus according to Clause 33, wherein said each of the plurality of imaging optics creates an image in front of the retina having an image magnification in a range from 5 to 20 or in a range from 25 to 100.

[0269] Clause 37. The apparatus according to Clause 24, wherein the image in front of the external portion of the retina comprises a modulation transfer function having an amplitude not less than 0.75 at a spatial frequency of 10 lp / mm and not less than 0.40 at a spatial frequency of 30 lp / mm, and optionally the modulation transfer function having an amplitude not less than 0.75 at a spatial frequency of 10 lp / mm and not less than 0.40 at a spatial frequency of 50 lp / mm.

[0270] Clause 38. The apparatus according to Clause 30, wherein each of the plurality of projection optics comprises imaging optics including collimating optics configured to form an image in front of the retina.

[0271] Clause 39. The apparatus according to Clause 30, wherein said projection optics comprise a single lens that simultaneously functions as collimating optics and imaging optics.

[0272] Clause 40. The apparatus according to Clause 30, wherein said projection optics comprise imaging optics to create an image in front of the external portion of the retina having a decentration not more than 30 degrees and a depth of focus not more than 1.0 D.

[0273] Clause 41. The apparatus according to Clause 39, wherein said optics create an image in front of the external portion of the retina having a decentration not more than 30 degrees, wherein a modulation transfer function of said image decreases by a minimum of 0.1 units for a defocus of 1.0 D, and optionally wherein the defocus of 1.0 D comprises an incremental defocus.

[0274] Clause 42. The apparatus according to Clause 24, wherein the plurality of light sources comprises a plurality of micro-displays.

[0275] Clause 43. The apparatus according to Clause 24, wherein the plurality of light sources comprises a plurality of light emitting diodes (LEDs).

[0276] Clause 44. The apparatus according to Clause 24, wherein each of said plurality of optical elements comprises a mirror assembly that collimates light emitted by a corresponding micro-display and directs a resulting light beam into a pupil of the eye, wherein said light beam is focused to form a peripheral image in front of the retina.

[0277] Clause 45. The device of clause 24, wherein each of the plurality of optical elements comprises a lens that receives light emitted by a corresponding microdisplay and directs a resulting light beam into a pupil of an eye, wherein the light beam is focused to form an image in front of the retina.

[0278] Clause 46. The device of clause 24, wherein the plurality of light sources generate multi-color illumination, and optionally wherein the plurality of light sources comprises a plurality of microdisplays that generate the multi-color illumination.

[0279] Clause 47. The device of clause 24, wherein the image is in front of the retina by about 0.5 mm to 2.0 mm.

[0280] Clause 48. The device of clause 24, wherein the image has a resolution of at least 10 lp / mm and optionally at least 30 lp / mm.

[0281] Clause 49. The device of clause 24, wherein the image has a magnification of no more than 200x and optionally no more than 100x.

[0282] Clause 50. The device of clause 24, wherein the image has a depth of focus of no more than 2.5 diopters, and optionally wherein the depth of focus is no more than about 0.9 mm.

[0283] Clause 51. The device of clause 24, wherein the image is projected with an eccentricity in a range from about 7.5 degrees to about 45 degrees and optionally in a range from about 15 degrees to about 45 degrees.

[0284] Clause 52. The device of clause 51, wherein the range is from about 15 degrees to about 30 degrees.

[0285] Clause 53. The device of clause 24, wherein the microdisplay illuminates the pupil with an illuminance in a range from about 100 cd / m 2 to 50,000 cd / m 2 , or in a range from about 0.1 cd / m 2 to 10 cd / m 2 .

[0286] Clause 54. The device of clause 24, wherein the image is focused at a location a distance in front of the peripheral retina, and the image comprises a depth of focus that is less than the distance and a spatial resolution that is greater than a spatial resolution of the peripheral retina at the location.

[0287] Clause 55. The device of clause 24, further comprising a sensor to receive input from a wearer when the contact lens has been placed on the wearer’s eye.

[0288] Clause 56. An eyeglass lens comprising a display, wherein the display projects images on the peripheral retina to reduce the progression of myopia.

[0289] Clause 57. The eyeglass lens according to clause 56, wherein the display comprises a microdisplay.

[0290] Clause 58. The eyeglass lens according to clause 56, wherein the display comprises a micro-projector coupled to the eyeglass frame at a location corresponding to the temple of the wearer.

[0291] Clause 59. The eyeglass lens according to clause 56, wherein the display comprises a near-eye display.

[0292] Clause 60. The eyeglass lens according to clause 56, wherein the display is configured to stimulate retinal ingrowth.

[0293] Clause 61. The eyeglass lens according to clause 56, wherein the display comprises a microdisplay and a micro-optics array.

[0294] Clause 62. The eyeglass lens according to clause 56, wherein the display enables clear viewing of the real world over a field of view ranging from + / - 2.0 to + / - 15 degrees, and optionally from about + / - 2.0 to + / - 12.5 degrees.

[0295] Clause 63. The eyeglass lens according to clause 61, wherein the display projects an image of the light source of the microdisplay with a myopic defocus ranging from 2.0D to 7.0D, and optionally from 2.0D to 5.0D.

[0296] Clause 64. The eyeglass lens according to clause 56, wherein the display projects images at an eccentricity relative to the fovea ranging from 15 to 40 degrees, and optionally from 20 to 30 degrees, in the peripheral region of the retina.

[0297] Clause 65. The eyeglass lens according to clause 56, wherein the lens comprises a plurality of near-eye displays to enable binocular stimulation of the peripheral retina.

[0298] Clause 66. The eyeglass lens according to clause 56, wherein the display transmits more than 80% of the light incident thereon over a field of view not less than + / - 5 degrees laterally and not less than + / - 7 degrees vertically, and optionally over a field of view not less than + / - 12 degrees laterally and not less than + / - 20 degrees vertically.

[0299] Clause 67. The eyeglass lens or device of any preceding clause, wherein the projected image moves to compensate for eye movements, and optionally wherein the projected image moves to provide stimulation to the overlap area of the retinal periphery in response to eye movements.

[0300] Clause 68. The eyeglass lens or device of any preceding clause, wherein the retinal periphery comprises an external location of the retina away from the macula.

[0301] Clause 69. The device of any preceding clause, further comprising a processor coupled to the plurality of light sources to control illumination of the plurality of light sources.

[0302] Clause 70. The device of any preceding clause, further comprising a wireless communication circuit operably coupled to the plurality of light sources to control illumination of the plurality of light sources.

[0303] Clause 71. The device of any preceding clause, further comprising a wireless communication circuit operably coupled to a mobile device for the wearer to control illumination of the plurality of light sources.

[0304] Clause 72. The device of any preceding clause, further comprising a wireless communication circuit operably coupled to the processor for a health care provider to program illumination cycles and intensities of the plurality of light sources.

[0305] Clause 73. The device of any preceding clause, wherein the device does not comprise a contact lens.

[0306] While the preferred embodiments of the application have been shown and described herein, it will be apparent to those skilled in the art that many changes, modifications, and substitutions can be made thereto without departing from the application. It is intended that the application embrace all such changes, modifications, and substitutions as fall within the scope of the specification. Although the present application has been described with reference to the above explanation to illustrate the preferred embodiments of the application, the description and illustrations are not intended to limit the application to the forms disclosed. One skilled in the art will be able to conceive variations, modifications, and alternatives, without departing from the application. Furthermore, it should be understood that all aspects of the application are not limited to the specific details described herein, which are dependent on a variety of conditions and variables. It should be understood that various alternatives to the embodiments of the application described herein can be employed in practicing the application. It is, therefore, intended that the application should cover by the appended claims any and all changes, modifications, variations, or alternatives that fall within the true spirit and scope of the application. The claims are intended to be construed as limiting the scope of the application.

Claims

1. An apparatus for providing stimulation to a retina of an eye, comprising: an eyeglass lens; a display on the eyeglass lens, the display projecting an image on a periphery of the retina to reduce progression of myopia of the eye; wherein the eyeglass lens comprises a central optical zone to provide emmetropia correction of the eye; the display comprises one or more projection optics coupled to one or more light sources to illuminate the retina with one or more defocused images, wherein the one or more projection optics are configured to project the one or more defocused images onto the retina, away from a central field, without reducing central vision; each of the one or more defocused images is configured to have an image structure corresponding to information or content of the image, and the information or content of the image is associated with a spatial frequency, the image comprising information or content in a spatial frequency range of 1 cycle per degree to 60 cycles per degree; and wherein the one or more defocused images formed on one or more regions of the retina comprise a resolution finer than a resolution of the retina at the one or more regions; the light beams are directed to the one or more regions of the retina at an angle relative to an optical axis of the eye so as to illuminate an outer portion of the retina away from the fovea with a resolution finer than a corresponding location of the retina; a depth of focus is configured to illuminate the retina with an appropriate amount of blurring of the image on the retina, a size of the spot is appropriately adjusted to provide a resolution finer than a resolution of the retina for the image formed in front of the retina.

2. The apparatus of claim 1, wherein, the one or more images comprise one or more of a still image or a dynamic image.

3. The apparatus of claim 2, wherein, the image comprises a dynamic image having a refresh rate in a range from 1 Hz to 200 Hz.

4. The apparatus of claim 1, wherein, the one or more images comprise one or more of a monochromatic light or a polychromatic light, the monochromatic light or polychromatic light comprising a wavelength in a range from 400 nm to 800 nm.

5. The apparatus of claim 1, wherein, the image has information or content in a spatial frequency range of 1 cycle per degree to 30 cycles per degree.

6. The apparatus of claim 1, wherein, the image comprises a contrast in a range from 99.9% to 2.5%.

7. The apparatus of claim 1, wherein, the image comprises a decentration in a range from 5 degrees to 40 degrees relative to the fovea.

8. The apparatus of claim 7, wherein, the image illuminates the retina in the range in a pattern that extends continuously 360 degrees around the fovea.

9. The apparatus of claim 7, wherein, the image illuminates a portion of the retina in the range.

10. The apparatus of claim 1, further comprising circuitry for stimulating the retina using the one or more images, the one or more images using temporal illumination, the temporal illumination comprising one or more of continuous illumination, discontinuous illumination, periodic illumination, or aperiodic illumination.

11. The apparatus of claim 10, wherein, the temporal illumination comprises periodic illumination having a duration in a range from 1 second to 24 hours.

12. The apparatus of claim 10, wherein, the temporal illumination comprises discontinuous illumination having a duration in a range from 1 second to 24 hours.

13. The apparatus of claim 10, wherein, The circuitry is configured to illuminate the retina when the subject is in one or more of a state of wakefulness, sleep, or drowsiness.

14. The device of claim 1, further comprising circuitry to stimulate a retina using the one or more images, the one or more images having a spatial illumination pattern, the spatial illumination pattern comprising one or more of a continuous spatial illumination pattern, a discontinuous spatial illumination pattern, a periodic spatial illumination pattern, or a non-periodic spatial illumination pattern.

15. The apparatus of claim 1, wherein, The one or more images comprise a luminance in a range from 1 Troland to 1000 Troland.

16. The apparatus of claim 1, wherein, The one or more projection optics are configured to project the one or more images having a luminance in a range from 100 nits to 50,000 nits or in a range from 1 nit to 10,000 nits.

17. The apparatus of claim 1, wherein, The one or more images correct for refractive error of the eye.

18. The apparatus of claim 1, wherein, The one or more images are defocused relative to one or more locations of the retina at which the one or more images illuminate the retina.

19. The apparatus of claim 18, wherein, The one or more images are myopically defocused in a range from 2.0D to 7.0D.

20. The apparatus of claim 18, wherein, The one or more images are hyperopically defocused in an amount in a range from 2.0D to 7.0D.

21. The apparatus of claim 1, wherein, The one or more projection optics comprise components of a light projection system.

22. The apparatus of claim 21, wherein, The light projection system comprises components of one or more of: a projector, an ophthalmic device, a mobile computing device.

23. The device of claim 21, further comprising a support coupled to the light projection system, the support comprising one or more of: an ophthalmic device, a mobile computing device, a wearable device, a spectacle frame.

24. The device of claim 1, comprising: wherein the one or more projection optics comprise a plurality of projection optics coupled to the plurality of light sources to project a plurality of images in front of the retina.

25. The apparatus of claim 24, wherein, The plurality of projection optics are arranged to project the plurality of images of the plurality of light sources to a plurality of peripheral regions of the retina of an eye with an eccentricity relative to a fovea of the eye in a range from 5 degrees to 30 degrees.

26. The apparatus of claim 24, wherein, Each of the plurality of projection optics is arranged to project an image that is myopically defocused relative to a surface of the retina, wherein the amount of defocus is in a range from 2.0D to 7.0D.

27. The apparatus of claim 24, wherein, The plurality of projection optics comprises a plurality of imaging optics optically coupled to the plurality of light sources to project the plurality of images in front of a surface of the retina.

28. The apparatus of claim 27, wherein, Each of the plurality of light sources has a maximum span of no more than 26 microns.

29. The apparatus of claim 27, wherein, Each of the plurality of projection optics comprises one or more of a mirror, a lens, or a light guide.

30. The apparatus of claim 29, wherein, Each of the plurality of imaging optics comprises one or more of a diffractive element, a Fresnel lens, or a compound Gabor lens.

31. The apparatus of claim 29, wherein, Each of the plurality of imaging optics has a maximum span in a range from 200 microns to 1.5 mm.

32. The apparatus of claim 29, wherein, Each of the plurality of imaging optics is aspherical and corrected for image aberrations.

33. The apparatus of claim 29, wherein, Each of the plurality of imaging optics includes a combination of a convex mirror and a concave mirror.

34. The apparatus of claim 32, wherein, Each of the plurality of imaging optics forms an image in front of an outer portion of the retina with a decentration in a range from 1 degree to 30 degrees from the fovea.

35. The apparatus of claim 32, wherein, Each of the plurality of imaging optics produces an image in front of the retina with an image magnification in a range from 5 to 20 or in a range from 25 to 100.

36. The apparatus of claim 24, wherein, The image in front of the outer portion of the retina includes a modulation transfer function with an amplitude not less than 0.75 at a spatial frequency of 10 lp / mm and not less than 0.40 at a spatial frequency of 30 lp / mm.

37. The apparatus of claim 29, wherein, Each of the plurality of projection optics includes an imaging optic including a collimating optic configured to form an image in front of the retina.

38. The apparatus of claim 29, wherein, The projection optics include a single lens that functions simultaneously as a collimating optic and an imaging optic.

39. The apparatus of claim 29, wherein, The projection optics include an imaging optic to create an image in front of an outer portion of the retina with a decentration not more than 30 degrees and a depth of focus not more than 1.0 D.

40. The apparatus of claim 38, wherein, The projection optics create an image in front of an outer portion of the retina with a decentration not more than 30 degrees, wherein a modulation transfer function of the image decreases by a minimum of 0.1 units for a defocus of 1.0 D.

41. The apparatus of claim 24, wherein, The plurality of light sources includes a plurality of micro-displays.

42. The apparatus of claim 24, wherein, The plurality of light sources includes a plurality of light emitting diodes (LEDs).

43. The apparatus of claim 24, wherein, Each of the plurality of projection optics includes a mirror assembly that collimates light emitted by a corresponding micro-display and directs a resulting light beam into a pupil of an eye, wherein the light beam is focused to form a peripheral image in front of the retina.

44. The apparatus of claim 24, wherein, Each of the plurality of projection optics includes a lens that receives light emitted by a respective micro-display and directs a resulting light beam into a pupil of an eye, wherein the light beam is focused to form an image in front of the retina.

45. The apparatus of claim 24, wherein, The plurality of light sources generates multi-color illumination.

46. The apparatus of claim 24, wherein, The plurality of images is at 0.5 mm to 2.0 mm in front of the retina.

47. The apparatus of claim 24, wherein, The plurality of images has a resolution of at least 10 lp / mm.

48. The apparatus of claim 24, wherein, The plurality of images has a magnification of not more than 200x.

49. The apparatus of claim 24, wherein, The plurality of images has a depth of focus of not more than 2.5 diopters.

50. The apparatus of claim 24, wherein, The plurality of images is projected with a decentration in a range from 7.5 degrees to 45 degrees.

51. The apparatus of claim 50, wherein, The range is from 15 degrees to 30 degrees.

52. The apparatus of claim 24, wherein, The plurality of light sources comprises a plurality of micro-displays illuminating the pupil with an illuminance in a range from 100 cd / m 2 to 50,000 cd / m 2 , or in a range from 0.1 cd / m 2 to 10 cd / m 2 .

53. The apparatus of claim 24, wherein, The plurality of images are focused at a location at a distance in front of the peripheral retina and the images comprise a depth of focus that is less than the distance and a spatial resolution that is greater than a spatial resolution of the peripheral retina at the location.

54. The apparatus of claim 1, wherein, The display comprises a microdisplay.

55. The apparatus of claim 1, wherein, The display comprises a micro-projector coupled to an eyeglasses frame at a location corresponding to a temple of the wearer.

56. The apparatus of claim 1, wherein, The display comprises a near-eye display.

57. The apparatus of claim 1, wherein, The display is configured to stimulate the retina to grow inwards.

58. The apparatus of claim 1, wherein, The display comprises a microdisplay and a micro-optics array.

59. The apparatus of claim 1, wherein, The display enables clear viewing of the real world over a field of view ranging from + / - 2.0 to + / - 15 degrees.

60. The apparatus of claim 58, wherein, The display projects an image of the light source of the microdisplay with a myopic defocus ranging from 2.0D to 7.0D.

61. The apparatus of claim 1, wherein, The display projects an image with an eccentricity relative to the fovea ranging from 15 to 40 degrees at the peripheral region of the retina.

62. The apparatus of claim 1, wherein, The eyeglasses lens comprises a plurality of near-eye displays so as to enable binocular stimulation of the peripheral retina.

63. The apparatus of claim 1, wherein, The display transmits more than 80% of the light incident thereon over a field of view that is not less than + / - 5 degrees laterally and not less than + / - 7 degrees vertically.

64. The apparatus of any one of claims 1 to 63, wherein, The projected image moves to compensate for eye movements.

65. The apparatus according to any one of claims 1 to 63, wherein, The periphery of the retina comprises an outer location of the retina away from the macula.

66. The apparatus of any one of claims 1 to 63, further comprising a processor coupled to the plurality of light sources to control illumination of the plurality of light sources.

67. The apparatus of any one of claims 1 to 63, further comprising wireless communication circuitry operably coupled to the plurality of light sources to control illumination of the plurality of light sources.

68. The apparatus of any one of claims 1 to 63, further comprising wireless communication circuitry operably coupled to a mobile device for enabling a wearer to control illumination of the plurality of light sources.

69. The apparatus of any one of claims 1 to 63, further comprising wireless communication circuitry operably coupled to a processor for enabling a health care provider to program illumination cycles and intensities of the plurality of light sources.

70. The apparatus according to any one of claims 1 to 63, wherein, The apparatus does not comprise contact lenses.

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