Contact lens device for myopia management

Abstract

The present disclosure is particularly directed to contact lens devices and / or methods for myopia treatment. The present disclosure is directed to modifying the incoming light by a contact lens, using a stop signal to slow the rate of progression of myopia. More particularly, the present disclosure is directed to a purposeful configuration of a non-circular, non-transparent aperture stop on the original base single-vision optic zone of a contact lens that can facilitate the redistribution of light energy into the oblique frequencies of the retinal image to provide an optical stop signal that prevents, reduces or controls the progression of refractive error of progressive myopia.

Description

[0001] Cross-references

[0002] This application claims priority to Australian Provisional Application Serial No. 2020 / 900607 entitled “Contact Lens Device”, filed on 1 March 2020, the entire contents of which are incorporated herein by reference. Technical Field

[0003] This disclosure particularly relates to contact lens devices and / or methods for myopia management. Specifically, this disclosure pertains to modifying incident light via a contact lens, which utilizes a stop signal to slow the rate of myopia progression. Background Technology

[0004] Humans are born farsighted; the length of the eyeball is too short for the eye's overall optical capacity. As a person grows from birth to adolescence, the eyeball continues to grow until the eye's refractive state stabilizes. Eye growth is controlled by feedback mechanisms and primarily regulated by visual experience to match the eye's line of sight with its length and maintain homeostasis. This process is called emmetropization.

[0005] The signals that guide the process of emmetropia begin at the retinal level. Retinal image characteristics are monitored by biological processes that modulate the signals to start or stop, accelerating or slowing down eye growth. Derailment from the emmetropia process leads to refractive errors such as myopia. The problem of myopia is rapidly increasing, and it is predicted that by 2050, half of the world's population may have myopia.

[0006] A simple pair of standard single-vision contact lenses can correct nearsightedness. While such devices can correct refractive errors, they do not address the underlying cause of vision deterioration related to excessive eye growth. There is still a need for contact lenses that can not only correct underlying refractive errors but also prevent excessive axial elongation of the eye.

[0007] Almost all contact lens design options available for slowing the progression of myopia include some form of optical manipulation of retinal image features, such as simultaneous defocusing, positive spherical aberration, manipulation of central and / or peripheral positive power optical zones, or manipulation of higher-order aberrations. One drawback of this optical design is that it impairs visual quality.

[0008] Given the impact of eyeglasses wear adherence on efficacy, a significant decrease in visual performance can foster poorer adherence, thus leading to poorer efficacy in delaying myopia progression. Therefore, what we need is an optical design that simultaneously corrects myopia and slows its progression without causing visual impairment related to controlling optical power.

[0009] Embodiments of this disclosure pertain to alternative methods or apparatuses for delaying myopia progression that do not utilize any kind of paraxial defocus, whether on-axis or off-axis, or do not use any positive spherical aberration, or any kind of optical blur as a stop signal.

[0010] definition

[0011] Unless otherwise defined, the terminology used herein is the same as that commonly used by those skilled in the art. The term "myopia" refers to an eye that has experienced myopia, is in the pre-myopia stage, or has been diagnosed with a refractive condition that is likely to progress to myopia.

[0012] The term “progressive myopia” refers to myopia that has been diagnosed as developing, which is measured by a change in refractive error of at least -0.25D / year or a change in axial length of at least 0.1 mm / year.

[0013] The term “pre-myopic eye” or “myopia-risk eye” refers to an eye that may be emmetropic or have low distance vision at the time, but is identified as having an increased risk of myopia based on the following factors: genetic factors (e.g., both parents are myopic) and / or age (e.g., being hyperopic at a young age) and / or environmental factors (e.g., time spent outdoors) and / or behavioral factors (e.g., time spent performing near tasks).

[0014] The term "optical stop signal" refers to a signal that can promote slowing down, reversing, braking, delaying, inhibiting, or controlling the growth of the eye and / or the refractive condition of the eye.

[0015] The term "contact lens" refers to a manufactured contact lens, whether soft, hard, or hybrid, that is fitted onto the wearer's cornea to affect the eye's optical performance, typically packaged in vials, blister packs, or the like. The term "orthokeratology" lenses can refer to contact lenses used to flatten the cornea to provide vision correction.

[0016] The term "optical zone" refers to the area on a contact lens that provides the specified optical effect. The term "optical center of a contact lens" refers to the geometric center of the optical zone of the contact lens. The terms "geometric" and "geometric center" have essentially the same meaning.

[0017] The term or phrase "single-beam optical region" or "essentially single-beam region or profile" can indicate that an optical region has a uniform luminous intensity distribution and may or may not have asphericity in the luminous intensity variation throughout the optical region. A single-beam optical region can be further classified to include components such as toric surfaces or astigmatism to correct distance-related refractive errors. Summary of the Invention

[0018] Some embodiments of this disclosure include soft and rigid contact lenses, including orthokeratology lenses, and / or methods for altering the characteristics of incident light entering the human eye. Some embodiments of this disclosure relate to the configuration, methods, and / or systems for contact lenses used to correct and treat refractive errors.

[0019] Some embodiments of this disclosure are designed to correct myopic refractive errors and simultaneously provide optical signals to stop further eye growth or myopia progression. Some embodiments of this disclosure particularly relate to contact lens devices and / or methods for myopia management. This disclosure pertains to slowing the rate of myopia progression by modifying incident light through contact lenses and utilizing optical stopping signals.

[0020] More specifically, this disclosure relates to a contact lens in which a non-circular, non-transparent region is intentionally configured as an aperture stop in other substantially single-vision optical regions, which can promote altered dot spread function and modulation transfer function on the retina; wherein the altered dot spread function and modulation transfer function on the retina can also be reflected by spectral characteristics of the retinal image. The light energy within the spectral characteristics is intentionally redistributed at tilt frequencies; this can serve as an optical stop signal to suppress, reduce, or control refractive errors in progressive myopia.

[0021] This invention relates to a device, system, and / or method for reducing the rate of myopia progression, and more particularly to an advanced contact lens having a non-circular, non-transparent region configured within the lens's optical region as an aperture stop. The invention also relates to a device, system, and / or method for altering retinal image characteristics by utilizing or introducing a non-circular, non-transparent region as an aperture stop in soft or rigid contact lenses. When an incident light beam passes through the eye and the contact lens of this disclosure, the image formed on the retina contains additional features in the retinal image tilt frequencies, or redistributes energy to the retinal image tilt frequencies. This results in an altered retinal image where the incident light energy beam is redistributed to the tilt frequencies, potentially providing a halting signal for the growth of myopia.

[0022] In some embodiments of this disclosure, the intended features of an effective non-circular, non-transparent region serving as an aperture stop can be introduced into rigid or soft contact lenses, wherein the aperture stop can be at least partially disposed on the front or rear surface of the contact lens or embedded in a matrix. In some examples where the aperture stop is disposed on the front or rear surface of the contact lens, conventional or routine printing techniques frequently used in the cosmetic contact lens industry can be applied. In other examples where the non-circular, non-transparent aperture is disposed within a matrix of material, laser etching or engraving methods are considered.

[0023] Certain embodiments of this disclosure envision various exemplary methods for the purposeful redistribution of energy to tilted frequencies that form an image on the retina of a myopic eye. This disclosure hypothesizes that by redistributing energy to tilted frequencies, the spectral characteristics of the retinal image formed using the methods and devices of this disclosure are simulated to resemble a retinal image obtained by viewing a natural scene, which can then generate a stopping signal to reduce the rate of myopia progression. The contact lenses of the proposed disclosure utilize a non-circular, non-transparent region intentionally designed as an aperture stop within a substantially single optical area to purposefully, at least partially, redistribute the incoming light energy beam to tilted directions within the spectral characteristics of the image formed on the central and / or peripheral retina.

[0024] Certain embodiments of this disclosure describe a contact lens for slowing, delaying, or preventing at least one of the development of myopia, wherein the contact lens includes an optical region and a non-optical region having an optical center; wherein the optical region includes at least the following: (i) a transparent region having a substantially single light, the transparent region being configured to substantially match the refractive error of the myopic eye, thereby providing a focused retinal image of an incident light beam entering the myopic eye. Wherein, spectral features are generated when the retinal image is characterized using a point spread function, an optical transfer function, a modulation transfer function, or a convolutional image simulation operation. (ii) a non-circular, non-transparent region surrounding the transparent region is configured to form an aperture stop of the contact lens; wherein the non-circular, non-transparent aperture stop of the contact lens is capable of at least partially redistributing the incident light to a plurality of tilted spatial frequencies of the spectral features, such that the redistributed spectral image simulates the spectral features of an image formed when viewing a natural scene. The redistributed spectral image differs significantly from the spectral characteristics of the artificial scene, which may be primarily controlled by information on horizontal and vertical frequencies. The optical stopping signal provided by the redistributed spectral image on the retina of a myopic eye can slow down the progression of myopia.

[0025] In some embodiments, the area of ​​the non-circular, non-transparent region used as the aperture stop can be at least 2.5 square millimeters, at least 5 square millimeters, at least 7.5 square millimeters, at least 10 square millimeters, or at least 12.5 square millimeters. In some embodiments, the area of ​​the transparent region having a substantially single-light distribution can be at least 6 square millimeters, at least 9 square millimeters, at least 12 square millimeters, at least 15 square millimeters, or at least 18 square millimeters.

[0026] In some embodiments, the non-circular opaque region used as the aperture stop can be off-center from the optical center of the contact lens, and the size of the off-center can be at least approximately 0.125 mm, at least 0.25 mm, at least 0.5 mm, at least 0.75 mm, or at least 1 mm. In some embodiments, the off-center direction of the non-circular opaque region can be horizontal, vertical, upward, or downward; in other embodiments, the off-center direction of the non-circular opaque region can also be in an inclined direction.

[0027] In other embodiments, the non-circular, non-transparent region used as the aperture stop can be generally similar to a variety of regular polygons: between 3 and 12 sides, between 5 and 12 sides, between 5 and 8 sides, between 5 and 10 sides, or between 6 and 14 sides. In yet another embodiment, the non-circular, non-transparent region can specifically exclude rectangular, square, or rhomboid shapes. In other embodiments, where the non-circular, non-transparent region includes a rectangular, square, or rhomboid shape, the non-circular, non-transparent region may need to be oriented in a rectangular, square, or rhomboid manner, and may need to be tilted. In some embodiments, a suitable orientation or stabilization system for the contact lens may be considered to position the lens at the desired tilt angle.

[0028] According to another embodiment of this disclosure, the aperture stop can be triangular, pentagonal, hexagonal, heptagonal, octagonal, or star-shaped. According to other embodiments of this disclosure, the boundary defining a non-circular opaque aperture stop can be configured as a non-linear line, such as a curve.

[0029] In other embodiments, the non-circular, non-transparent region used as the aperture stop can be configured to be translucent, partially opaque, or substantially opaque. To facilitate the incorporation of translucent, partially opaque, or substantially opaque non-circular, non-transparent regions into contact lenses, conventional trade instruments used in the cosmetics industry can be considered.

[0030] In yet another embodiment, the non-circular, non-transparent region used as the aperture stop is configured such that its diameter is significantly larger than the physiological pupil of a myopic eye measured under scotopic, moderate scotopic, or dim lighting conditions.

[0031] In some embodiments of this disclosure, the transparent region may include spherical power and / or astigmatism power; in some other embodiments, the transparent region may be further configured to have additional positive or negative spherical aberration to optimize visual performance in myopic eyes. In some embodiments, the image scene formed by one or more embodiments of this disclosure for comparing and / or evaluating the performance of spectral features of retinal images may include various images representing natural scenes. For example, forest scenes, mountain scenes, wilderness scenes, beach scenes, coastal scenes, river scenes, or waterfall scenes.

[0032] In some embodiments, the image scene formed by one or more embodiments of this disclosure for comparing and / or evaluating the performance of spectral features of retinal images may include various images representing man-made scenes. For example, indoor scenes, street scenes, high-rise building scenes, cityscape scenes, highway scenes, office scenes, or portrait scenes.

[0033] In some embodiments, the contact lenses of this disclosure are configured to provide the wearer with sufficient field of vision that is substantially indistinguishable from conventional or traditional single-vision contact lenses that do not contain non-circular, non-transparent areas as disclosed in the present disclosure. In other embodiments, the lenses may be configured to provide the wearer with sufficient visual performance that is substantially indistinguishable from conventional or traditional single-vision contact lenses that are substantially without non-circular, non-transparent areas as disclosed in the present disclosure.

[0034] In another embodiment, the lens is configured to provide a visible light transmittance that is in the range of at least 80%, at least 85%, at least 90%, or at least 95% provided by conventional or traditional single-vision contact lenses currently disclosed without non-circular, non-transparent areas.

[0035] In some embodiments, the optical performance evaluation of the contact lens examples disclosed herein may include: (i) using at least one pupil diameter between 3 mm (inclusive) and 6 mm (inclusive); (ii) using at least one visible light wavelength between 460 nm (inclusive) and 760 nm (inclusive); (iii) using at least one field of view angle between 0 degrees (inclusive) and 30 degrees (inclusive); (iv) calculating the retinal image using an image quality metric that simulates the retinal image using at least one of a point spread function, an optical transfer function, a modulation transfer function, or a standard convolution operation; and (v) using a schematic diagram or a physical or desktop simulated eye.

[0036] In some examples, in one or more embodiments, the performance of one or more embodiments of this disclosure is determined by comparing the spectral characteristics of retinal images formed on a schematic, physical or desktop model eye with spectral characteristics of images representing natural or artificial scenes.

[0037] According to one embodiment, this disclosure addresses contact lenses configured with design features, such as a non-circular, non-transparent aperture stop within a basic single optical area, which can overcome the limitations of the prior art by providing a retinal image profile similar to that formed when viewing an object from a natural scene.

[0038] According to one embodiment, this disclosure addresses contact lenses configured with design features, such as a non-circular, non-transparent aperture stop within a substantially single optical area, which can overcome the limitations of the prior art by providing a retinal image profile that is substantially different from the retinal image formed when viewing an object from an artificial scene.

[0039] In another embodiment, the invention relates to an orthokeratology lens for at least slowing, delaying, or preventing myopia progression. In one embodiment, the orthokeratology lens includes an anterior surface, a posterior surface, a non-circular posterior optical region, an optical center; and a non-circular posterior optical region surrounding the optical center, configured to flatten the corneal surface to provide at least partial and sufficient foveal correction, and further configured with a non-circular aperture to provide at least partially an increase in energy distributed in the tilt direction of the spectral characteristics of the retinal image, thereby providing a stopping signal to reduce the rate of myopia progression.

[0040] Some embodiments of this disclosure also relate to an orthokeratology contact lens configured to effectively create a non-circular effective optical aperture within a treatment area to correct distance refractive errors in the wearer. The effective non-circular aperture alters the transmission characteristics of incident light, causing incident light energy to be redistributed to tilted frequencies of the spectral characteristics to mimic the spectral features of an image formed when viewing a natural scene. In other embodiments related to the orthokeratology contact lens, its posterior surface may be configured to effectively create an elliptical effective aperture with a treatment area to correct distance refractive errors in the wearer, and may be tilted. For example, the position of the elliptical effective aperture may be between 25 degrees and 75 degrees, or between 110 degrees and 160 degrees. The effective non-circular aperture, configured to be tilted, purposefully alters the transmission characteristics of incident light, thereby redistributing energy to multiple tilted frequencies of the spectral characteristics.

[0041] The spectral characteristics of retinal images with energy redistributed to tilted frequencies mimic the spectral characteristics of images obtained when viewing a natural scene. This disclosure assumes that the experience of retinal images similar to those of natural scenes with tilted frequencies has a protective effect against progressive myopia.

[0042] The embodiments disclosed in this invention address the ongoing need for enhanced-function ophthalmic lenses that can inhibit or slow the progression of myopia while providing adequate visual performance for the wearer. Various aspects of the embodiments disclosed in this invention address this need of the wearer. Attached Figure Description

[0043] Figure 1 The spectral features of two distinct visual scenes are shown, as disclosed in this paper: one representing a natural scene and the other representing a man-made scene.

[0044] Figure 2 The spectral characteristics of fourteen (14) different types of visual scenes are shown, along with representative samples of seven (7) natural scenes and seven (7) man-made scenes, as disclosed herein.

[0045] Figure 3 The single-pass point spread function at the retina is shown as disclosed herein when a collimated beam passes through circular, elliptical, triangular, and square apertures of the eye, which are optical systems.

[0046] Figure 4 The single-pass point spread function at the retina is shown as disclosed herein when a collimated beam passes through a pentagonal, hexagonal, octagonal, and irregular hexagonal shaped aperture of the eye, which serves as an optical system.

[0047] Figure 5 The outlines / sketches of two artificial scenes are shown: (i) representing a city skyline; and (ii) representing an indoor office environment.

[0048] Figure 6 These are front and cross-sectional views of exemplary contact lens embodiments disclosed herein, and are not drawn to scale. The non-circular, non-transparent optical aperture stop includes a triangular transparent region within the optical area.

[0049] Figure 7 As disclosed herein, Figure 6 The spectral features of a retinal image formed by one of the disclosed exemplary embodiments installed in an illustrative myopia model eye are described. As disclosed herein, two spectral features are obtained in two different configurations: (a) having and (b) not having non-circular, non-transparent aperture stop features.

[0050] Figure 8 These are front and cross-sectional views of exemplary contact lens embodiments disclosed herein, not drawn to scale. The non-circular, non-transparent optical aperture stop includes a regular hexagonal transparent region within the optical area.

[0051] Figure 9 The image shows an eye fitted onto a schematic myopia model. Figure 8 The spectral features of a retinal image formed by one of the exemplary embodiments disclosed herein. As disclosed herein, two spectral features are obtained in two different configurations, (a) having and (b) not having non-circular, non-transparent aperture stop features.

[0052] Figure 10 These are front and cross-sectional views of exemplary contact lens embodiments disclosed herein, not drawn to scale. The non-circular, non-transparent optical aperture stop includes a star-shaped transparent region within the optical area.

[0053] Figure 11 The image shows an eye fitted onto a schematic myopia model. Figure 10The spectral features of a retinal image formed by one of the exemplary embodiments disclosed herein. As disclosed herein, two spectral features are obtained in two different configurations, (a) having and (b) not having non-circular, non-transparent aperture stop features.

[0054] Figure 12 The views shown are front and cross-sectional views of exemplary contact lens embodiments disclosed herein and are not drawn to scale. The non-circular, non-transparent optical aperture stop includes a Maltese cross-shaped transparent area within the optical region.

[0055] Figure 13 The image shows an eye fitted onto a schematic myopia model. Figure 12 The spectral features of a retinal image formed by one of the exemplary embodiments disclosed herein. As disclosed herein, two spectral features are obtained in two different configurations, (a) having and (b) not having non-circular, non-transparent aperture stop features.

[0056] Figure 14 This is a cross-sectional front view of an exemplary embodiment of an orthokeratology rigid contact lens not disclosed herein, and is not drawn to scale. Detailed Implementation

[0057] As background to the present disclosure, a detailed discussion of the prior art and generally concerned topics is provided to illustrate the disclosed embodiments, and further distinguishes the advancements anticipated by this disclosure relative to the prior art.

[0058] Any material provided herein should not be construed as an admission that it refers to previously disclosed, known, or partially known common knowledge, as well as the various embodiments and / or claims set forth in this disclosure and in priority of the claims.

[0059] The following description provides several embodiments that share the general features and characteristics of this disclosure. It should be understood that one or more features of one embodiment may be combined with one or more features of any other embodiment to form further embodiments.

[0060] This disclosure is described in detail with reference to one or more embodiments, some of which are illustrated and supported by the accompanying drawings. Examples and embodiments are provided by way of explanation and should not be construed as limiting the scope of this disclosure.

[0061] The terms “comprising,” “containing,” “including,” “having,” “including,” “comprise,” or any variation thereof are intended to indicate a non-exclusive inclusion, such as an apparatus, method, process, or device, which includes a list of independent elements that includes not only the listed elements but also other elements not directly listed, as well as equivalents that are conventionally known or obvious to those skilled in the art.

[0062] Unless otherwise specifically described, the structures, arrangements, applications, proportions, elements, materials or components used in the practice of this invention, or otherwise particularly suited to a particular environment, manufacturing specifications, design parameters or other operational requirements without departing from the scope of this invention, may be varied and are intended to be included in this disclosure.

[0063] Throughout this disclosure, various exemplary embodiments of the invention known to the inventors at this time are disclosed. These embodiments and patterns are not intended to limit the scope, applicability, or configuration of the invention in any way. Rather, the following disclosure is intended to teach exemplary embodiments, patterns, and operational practices of any equivalent patterns or embodiments known or obvious to those skilled in the art. Furthermore, all included illustrations are non-limiting depictions of exemplary embodiments and patterns, which can similarly be used for any equivalent patterns or embodiments known or obvious to those skilled in the art. In this section, the disclosure will be described in detail with reference to one or more embodiments, some of which are illustrated and supported by the accompanying drawings. Examples and embodiments are provided by way of explanation and should not be construed as limiting the scope of this disclosure. The functional and structural information disclosed herein should not be construed as limiting in any way, but should only be construed as the basis for teaching those skilled in the art to adopt the disclosed embodiments and variations of those embodiments in various ways. Subtitles and related subject headings used in the detailed description section are included only for the reader's convenience and are in no way intended to limit the subject matter found throughout the invention or the claims of this disclosure. Furthermore, subtitles and related subject headings should not be used in interpreting the claims or the scope of the claims.

[0064] The classification of complex visual stimuli involving both natural and man-made scenes continues to challenge the human visual system. Spatial domain analysis can be used to understand the characteristics of these visual scenes, for example, by describing a scene based on pixel brightness, luminance, intensity, or color as a function of pixel spacing. Conversely, Fourier domain analysis can also be used to analyze scenes, which essentially involves decomposing the visual scene into a dual representation created using the amplitude and phase spectra of the visual scene. The amplitude spectrum corresponds to the distribution of luminance contrast across spatial frequencies and directions, while the phase spectrum corresponds to the spatial relationships between spatial frequencies within the visual scene. The magnitude of a luminance variation in a visual scene relative to its average luminance is called luminance contrast.

[0065] The visual system utilizes low-level features such as spatial frequency and brightness contrast for recognition, and from a neurobiological perspective, cells at the retinal and visual cortex levels are known to respond to brightness contrast, spatial frequency, and orientation. The coarse information contained in the lower spatial frequencies of an image conveys a plausible interpretation of the visual scene. This initial coarse information further guides the processing of higher spatial frequencies to provide finer information about the visual scene at the individual's visual cortex.

[0066] Fourier analysis of visual scenes captures a significant amount of image redundancy because the power spectrum of a visual scene (i.e., the square of its amplitude spectrum) provides a direct measure of its autocorrelation. Certain portions of this disclosure focus on Fourier analysis of visual scenes of both natural and man-made scenes. In particular, the paper entitled “Statistical Information of Natural Image Categories” by Torralba and Oliva (in Computational Neural Systems, Vol. 14, 2003, pp. 391–412) is cited in full as a reference. The average power spectrum can be modeled using polar coordinates, in which the shape of the spectrum depends primarily on directional features within the visual scene or image.

[0067] Throughout this disclosure, this may be referred to as the spectral features of a visual scene or image, particularly the characteristics of the spectral features discussed herein. The characteristics of the spectral features relevant to this invention include the shape of the spectral features and the energy distribution in the horizontal and vertical directions compared to the energy distribution in the tilt direction. In real-world visual scenes (including natural and man-made scenes), the vertical and horizontal directions are more frequent than the tilt direction. In other words, whether in natural or man-made scenes, the spectral features of real visual scenes have more energy distribution in the horizontal and vertical directions than in the tilt direction. Upon close examination of the tilt direction within the spectral features of natural and man-made visual scenes, it can be noted that the tilt direction is more frequent in natural scenes than in man-made scenes. Furthermore, in some man-made scenes, the tilt direction may be almost non-existent or very small, and can be ignored.

[0068] Figure 1 This text is reproduced from an existing technical publication [Torralba et al., “Statistics on the Categories of Natural Images”, Computer Neural Systems, Vol. 14 (2003), p. 394], the full text of which is incorporated herein by reference. Figure 1The spectral features of two different types of visual scenes are highlighted: a representative sample (101) obtained by averaging a large number of images of a natural scene, and another sample (102) obtained by averaging a large number of images of a man-made scene. Post-processing of the large number of representative natural and man-made images results in the depicted spectral features (101 and 102). The two contour lines in the spectral features represent 50% (inner) and 80% (outer) of the energy captured in the spectral features. The markers on the x and y axes of 101 and 102 represent arbitrary spatial frequency thresholds of 0.1 periods per pixel. The spatial frequency scale used in this example is normalized. The significant difference between 101 and 102 can be attributed to isotropy or lack of anisotropy (i.e., anisotropy) in the spectral features. The representative natural images provide more isotropic spectral features through the energy components observed in the horizontal, vertical, and tilt directions. In contrast, the man-made representative scene provides anisotropic spectral features and captures the least energy in the tilt direction. When considering man-made scenes, more relative energy is captured in the horizontal direction of the spectral features at smaller scales of difference. On the other hand, when considering natural scenes, more relative energy is captured in the vertical direction of the spectral features.

[0069] This disclosure envisions that the anisotropic distribution of orientation in an image could have the ability to modulate the neurobiology of a premyopic or myopic eye when the eye is primarily exposed to one type of image to another type of scene. For example, a myopic eye exposed to more man-made scenes might produce appropriate neurobiological changes to adapt to the corresponding visual dynamics.

[0070] In other words, this disclosure takes into account that artificial scenes or scenes lacking tilt frequencies can stimulate eye growth. Conversely, when the eye is exposed to natural images or images that provide tilt frequencies, these images may provide optical stopping signals, thereby slowing down eye growth or myopia development.

[0071] Figure 2 Also reproduced from existing publications [Torralba et al., “Statistics on the Categories of Natural Images”, Computer Neural Systems, Vol. 14 (2003), p. 395], the full text of which is incorporated herein by reference. Figure 2 The spectral features of approximately 14 different scene types are presented, including 7 representative scenes of natural origin and 7 man-made scenes. Post-processing of 14 representative images in each category (e.g., averaging of power spectra) produces the depicted spectral features. Figure 2The diagram further highlights different contour plots for 14 spectral features, where the three contour lines in each feature represent 60%, 80%, and 90% of the captured energy. The sum of the squares of the Fourier components forms the contour plot, which describes the distribution of the total energy. Although the representative scene depicts a distant visual scene, the concept can be extended to the spectral features of intermediate or near-distance visual scenes. For example, viewing computers, laptops, tablets, books, smartphones, etc., in an indoor setting.

[0072] As noted in this paper, the average power spectra from 14 different scene categories exhibit significantly different orientations and spatial frequency distributions. The differences between the various man-made categories lie primarily in the relationship between horizontal and vertical profiles at different scales, and the energy dispersed along the tilt direction of the spectral features is very small. However, the spectral features of natural environments appear to have much greater variation in spectral shape. When considering the level of their basic categories, such as forest scenes versus urban scenes, the spectral features of some individual scene categories differ significantly. From this, it is noted that… Figure 2 In contour maps, the dominant spatial proportions and orientations are very typical scene categories, representing different volumes or depth ranges. The spectral features of images of large scenes are primarily determined by the horizontal direction, such as beach scenes versus coastal scenes. When the scene background becomes closer to the observer, for example, when comparing images of mountains with images of enclosed natural objects, the spectral features become more isotropic and appear denser at high spatial frequencies. The shape of the spectral features in natural environments seems to be related to the proportion or size of the main components of the image; for example, the texture observed in a forest scene is finer, while the texture observed in a waterfall is coarser.

[0073] This disclosure hypothesizes that differences between natural and artificial images may explain the likelihood of progressive myopia. Furthermore, this disclosure envisions that anisotropic energy distribution within the spectral characteristics of images formed on the retina, or spectral characteristics lacking tilt orientation, can modulate the neurobiological performance of the eye when pre-myopic or myopic eyes are primarily exposed to images or scenes ranging from one type to another. For example, myopic eyes exposed to more artificial scenes than natural scenes may develop appropriate neurobiological changes to adapt to the corresponding visual dynamics. For instance, a hypothesis supported by population-based evidence or observations is that children living or growing up in rural areas, villages, small towns, or the countryside are less likely to develop myopia compared to their peers living or growing up in cities or modern urban areas.

[0074] This invention proposes an alternative method to delay the progression of myopia by intentionally introducing or increasing energy diffusion into the tilted dimension of the retinal spectral features using a non-circular, non-transparent aperture stop on a single-vision contact lens as disclosed herein. In some examples, the intentional introduction or increase of energy diffusion into the tilted dimension of the retinal spectral features may be limited to a specific area on the retina, or may not be limited to any specific area on the retina. In some embodiments, the contact lens may include a soft contact lens, while in another embodiment, the contact lens may refer to a gas-permeable or rigid contact lens worn during the day or night for orthokeratology (flattening and reshaping the anterior surface of the cornea). Another embodiment of this disclosure includes an alternative method for delaying myopia by using a specially designed orthokeratology lens with a dedicated posterior surface design discussed herein, utilizing a non-circular flattened region on the cornea, configuring the orthokeratology lens to provide a non-circular treatment area, and intentionally increasing energy dispersion in the tilted dimension of the retinal spectral features. In such examples, it should be understood that the non-circular treatment area of ​​the flattened cornea can create a quasi-aperture. In other words, in this case, the hole is not formed by an opaque boundary, but by a change in corneal refractive power that is not circular, and is referred to as a quasi-hole in this paper.

[0075] For example, when the eye is exposed to more artificial scenes without tilt frequencies, whether in distant and / or near visual environments, appropriate neurobiological changes may occur to adapt to this corresponding visual dynamics, thereby further accelerating myopia. In other words, the present invention discloses that artificial scenes or scenes lacking tilt frequencies can further stimulate eye growth. Conversely, when the eye is exposed to images with energy distributed at tilt frequencies, a halting signal for eye growth may be generated.

[0076] Cone and rod receptors of varying sizes and spacing are distributed in the central and peripheral retina. In some embodiments of this disclosure, power spectral analysis of the visual scene may also take these factors into account. Furthermore, there may be an interaction between the power spectrum and the wavelength spectrum of the visual scene.

[0077] The wavelength spectrum of a visual scene includes the wavelength characteristics of the incident light. In some visual scenes, the wavelength may be predominantly biased towards the blue end of the visual spectrum, including approximately 420 nm and 490 nm. In other visual scenes, the wavelength may be predominantly biased towards the green band of the visual spectrum, including approximately 500 nm and 590 nm.

[0078] In other visual scenarios, the wavelengths may be predominantly biased towards the red end of the visual spectrum, approximately 600 nm and 760 nm. In still other visual scenarios, the wavelengths may be predominantly biased towards the human cone sensitivity function, a non-linear function with a peak sensitivity around 555 nm.

[0079] A contact lens device or method, based on the use of a non-circular, non-transparent aperture stop in a single-vision optical region under other circumstances, can provide a stop signal that delays or stops the growth rate of the eye or the wearer's refractive error state, and can promote changes in the point spread function and modulation transfer function describing the energy distribution on the retina; wherein the energy distribution on the retina forming the changed point spread function is such that energy is distributed at tilt frequencies, which can be used as an optical stop signal to suppress, reduce or control progressive myopic refractive errors.

[0080] This invention relates to a device and / or method for slowing the progression of myopia, and more particularly to an advanced contact lens having a non-circular, non-transparent aperture stop configured in the optical region of the designed lens, which can purposefully introduce energy into the tilt frequency of the retinal spectral characteristics, wherein the altered retinal image can provide a stopping signal for the growth of myopia.

[0081] This disclosure also relates to an orthokeratology contact lens configured to produce a non-circular effective aperture to correct distance-related refractive errors in the wearer. The effective non-circular aperture alters the transmission characteristics of incident light, artificially introducing tilt frequencies that are otherwise only observable when viewing natural scenes. These tilt frequencies may generate a stopping signal to reduce the progression of myopia.

[0082] Figure 3 The retinal point spread functions obtained when a collimated beam passes through circular (301), elliptical (302), triangular (303), and square (304) apertures of a schematic model eye are shown. The on-axis point spread transfer function of a schematic model eye configured with a circular aperture stop or pupil is shown in 311. As noted here (311), the energy is distributed rotationally symmetrically along all meridians, including the horizontal, vertical, and tilt directions. Unlike the retinal point spread function observed using a circular aperture (301), the retinal point spread function obtained using an elliptical aperture stop or pupil is rotationally asymmetrical, particularly showing a variation between the horizontal and vertical meridians. Furthermore, using a triangular aperture stop or pupil within the schematic eye redistributes energy to the tilt frequency of its retinal point spread function (313). On the other hand, the retinal point spread function (314) observed using a square aperture (304) completely reduces or weakens the tilt frequency.

[0083] As contemplated by this disclosure, a triangular aperture (303) and its corresponding retinal dot spread function (313) will preferably be configured in the device disclosed herein, rather than a square aperture (304), because the corresponding retinal dot spread function (314) fails to show tilt frequencies in images projected from natural scenes.

[0084] In some other embodiments of this disclosure, the orientation of the polygonal pupil can be configured to selectively reduce or weaken a particular tilt frequency at other tilt, horizontal, or vertical frequencies.

[0085] Figure 4 The retinal point spread function observed when a collimated beam passes through pentagonal (401), hexagonal (402), octagonal (403), and irregular hexagonal (404) apertures of a schematic model eye is shown. The on-axis point spread function of a schematic model eye configured with pentagonal, hexagonal, octagonal, and irregular hexagonal aperture stops or pupils is shown in 411, 412, 413, and 414, respectively. As contemplated in this disclosure, pentagonal (401), hexagonal (402), octagonal (403), and irregular hexagonal (404) apertures and their corresponding point spread functions (411, 412, 413, and 414, respectively) would be preferred aperture types for optics configured within the intended optical devices (i.e., contact lenses) disclosed herein. In this example, using such apertures redistributes energy to tilt frequencies, potentially simulating optical performance obtained when viewing natural images or visual scenes projected from natural scenes. In some other embodiments, the orientation of the polygonal pupil can be configured to selectively reduce or weaken specific tilt frequencies at other tilt, horizontal, or vertical frequencies.

[0086] Figure 5 Two sketches of artificial scenes are presented, used to evaluate the performance of spectral features in retinal images formed by one or more embodiments. The first artificial scene is a sketch representing a city skyline, and the second is a sketch representing an indoor office environment. For ease of evaluation, [the following is a simplified description of the sketches]. Figure 5 Two artificial scenes are considered as source bitmap files, which are convolved with a point spread function array computed at the retina of the schematic model eye, the point spread function array spanning a certain field of view on the retina. When using one or more embodiments of this disclosure to correct a suitable schematic myopic model eye, as in Embodiments 1 to 5 herein (… Figures 6 to 13 As described above, its performance was obtained. The grid sampling used to calculate the point spread function was set to 65536 (256x256 array). The performance evaluations described in Examples 1-4 were performed under different configurations, including different pupils, wavelengths, and field of view angles.

[0087] The calculation of the spectral features for each embodiment of Examples 1 to 4 includes at least the following steps: (i) calculating the source bitmap (e.g., Figure 5 (i) Oversample one of the two artificial images by at least a multiple of 2; (ii) Determine at least the number of point spread functions to be computed in each direction within the desired field of view, wherein the number of point spread functions in each direction within the desired field of view is at least an 11×11 array; (iii) Thirdly, compute at least an 11×11 array grid of point spread functions at the desired field of view on the retina of an illustrative model eye equipped with various embodiments of the present disclosure; wherein the array grid of point spread functions is computed using Huygens' diffraction principle, which takes into account the aberrations of the system and the diffraction effects around the edges of the arbitrary aperture stop shape of the present disclosure. (iv) Then, for each pixel in the modified source bitmap, interpolation is performed on each point spread function within the array grid of point spread functions; wherein, at each pixel, the effective point spread function is convolved with the modified source bitmap to determine the resulting distorted bitmap image; wherein the final bitmap image I(x, y) is ultimately scaled and stretched to account for the desired image pixel size, distortion, and lateral aberration (if any); (v) Fourier domain analysis is performed on the resulting bitmap image I(x, y), and the normalized power spectrum is derived using the formula in Equation 1-2 to obtain the spectral characteristics; (vi) Finally, the data within the normalized power spectrum obtained by Equation 1-2 can be rescaled so that at least 60%, 70%, or 80% of the energy captured within the power spectrum can be preserved.

[0088] I fft (x,y)=abs(fftshift(fft2(I(x,y))))-Equation 1

[0089]

[0090] An illustrative model eye was used to calculate the spectral characteristics of exemplary embodiments of the present disclosure. Table 1 lists the prescription parameters of the illustrative model eye used to calculate the spectral characteristics. The prescriptions in Table 1 should not be construed as mandatory methods to demonstrate the effectiveness of the intended exemplary embodiments of the present disclosure.

[0091] This is merely one of many methods that can be used by those skilled in the art for optical simulation purposes. In other examples, lens designers may also modify parameters of various elements of the model eye; for example, the cornea, lens, retina, media, or combinations thereof, to help better simulate the described effects. For example, other illustrative model eyes, such as those of Atchison, Escudero-Navarro, Liou-Brennan, Polans, and Goncharov-Dainty, may be used alternatively to demonstrate the effects of other embodiments. In other examples, a physical or desktop model eye may be used instead of the illustrative model eye.

[0092]

[0093] Table 1: Schematic diagram of the prescription for the myopia model of -3DS.

[0094] The illustrative model eye in Table 1 is corrected using a conventional or traditional single-vision contact lens; the optical region diameter of the single-vision lens is approximately 6 mm, smaller than that of a conventional single-vision contact lens. The following parameters are used to simulate a single-vision contact lens: anterior surface radius of 8.675 mm, asphericity Q of zero, and posterior surface radius of 8.13, asphericity Q of -0.13. To simulate one or more embodiments of this disclosure, as shown in Examples 1 to 4 described herein, the transmission characteristics of their optical regions are altered.

[0095] Example 1

[0096] Figure 6 A front view of an exemplary contact lens embodiment is shown, not drawn to scale. The front view shows the optical region (601), the lens diameter (602), and design features (603a to 603c), namely the non-circular, non-transparent feature of the aperture stop. In this example, the lens diameter is approximately 14 mm, and the optical region is designed to be substantially single-vision refractive and has a diameter of approximately 6 mm.

[0097] In this example, the displayed non-circular, opaque region is an omitted area within a circle with a diameter of 6 mm inscribed in an equilateral triangle. The three sides of this equilateral triangle are defined as having a length of 2*R*cos(30 degrees), where R = 3 mm. In this example, the area of ​​the transparent region within the optical region defined by the equilateral triangle is approximately 11.66 square millimeters. In this example, the area of ​​the non-circular, opaque region is approximately 16.6 square millimeters.

[0098] Figure 7 It shows Figure 6One of the exemplary embodiments disclosed herein is the spectral characteristics of a retinal image formed on an illustrative myopic model eye as described in Table 1.

[0088] The single-vision contact lens described in the paragraph is configured in two different configurations, (a) without any expected non-circular, non-transparent features, and (b) having... Figure 6 The anticipated non-circular, non-transparent aperture stop feature described in (603) is used. When compared with the spectral features of a retinal image (701) obtained from a single-vision contact lens without any features of this disclosure, the use of the non-circular, non-transparent aperture stop (603) configured within the single-vision contact lens helps to redistribute light energy to the tilt frequencies of the spectral features of the retinal image (702), triggering a stop signal to the progressively myopic eye. In this example, the spectral features represent 60% of the energy captured in the power spectral analyses (701 and 702) described herein. In other examples, additional power spectral analyses may be required to include at least 70% or 80% of the captured energy within the spectral features. In this example, the following parameters were used for calculation: (a) a pupil diameter of 5 mm for the model eye; (b) a monochromatic wavelength of 0.589 μm; (c) a field of view of 15 degrees; and (d) Figure 5 The indoor artificial scene described in (501).

[0099] Example 2

[0100] Figure 8 A front view of an exemplary contact lens embodiment is shown, not drawn to scale. The front view shows the optical region (801), the lens diameter (802), and design features (803a to 803f), namely the non-circular, non-transparent feature of the aperture stop. In this example, the lens diameter is approximately 14.2 mm, and the optical region is designed to be substantially monocularly refractive and has a diameter of approximately 6 mm.

[0101] In this example, the characteristic non-circular opaque region is an omitted area within a 6mm circle inscribed in a regular hexagon, whose six sides have a defined length R, where R = 3mm. In this example, the area of ​​the transparent region within the optical region defined by the regular hexagon is approximately 23.38 square millimeters. In this example, the area of ​​the non-circular opaque region is approximately 4.88 square millimeters.

[0102] Figure 9 It shows Figure 8 One of the exemplary embodiments disclosed herein is the spectral characteristics of a retinal image formed on an illustrative myopic model eye as described in Table 1.

[0088] The single-vision contact lens described in the paragraph is configured in two different configurations, (a) without any expected non-circular, non-transparent features, and (b) having Figure 8The expected non-circular, non-transparent aperture stop feature (803) described herein. When compared with the spectral features of a retinal image (901) obtained from a single-vision contact lens without any features of this disclosure, the use of the non-circular, non-transparent aperture stop (803) configured within the single-vision contact lens helps to redistribute light energy to the tilt frequencies of the spectral features of the retinal image (902), triggering a stop signal to the progressively myopic eye. In this example, the spectral features represent 70% of the energy captured in the power spectral analysis (901 and 902) described herein. In other examples, additional power spectral analysis may be required to include at least 50% or 80% of the captured energy within the spectral features. In this example, the calculations were performed using the following parameters: (a) a pupil diameter of 5 mm for the model eye; (b) a multicolor wavelength source representing a photometric photometric function; (c) a field of view of 20 degrees; and (d) Figure 5 The indoor artificial scene described in (501).

[0103] In this example, using a transparent region with a regular hexagonal aperture may result in a non-circular, non-transparent region that is too narrow to be effective in all situations. Either too much light is blocked, or the natural pupil shape causes the aperture to cover the exposed feature under consideration. In such cases, the design feature can be optimized to address the issue of variable pupil size due to varying lighting conditions that the wearer may experience in daily life. For example, one method of optimizing the design feature may include separating the six sides of the hexagonal aperture (803a to 803f) and configuring them to have different distances from the center. At least one edge will affect the power spectrum while maintaining some modulation of the luminous flux. Alternatively, in some other embodiments, optimization of this design feature may include an off-center hexagonal (803) aperture.

[0104] Example 3

[0105] Figure 10 A front view of an exemplary contact lens embodiment is shown, not drawn to scale. The front view shows the optical region (1001), the lens diameter (1002), and design features (1003a to 1003f), namely the non-circular, non-transparent feature of the aperture stop. In this example, the lens diameter is approximately 13.8 mm, and the optical region is designed to be substantially monocularly refractive and has a diameter of approximately 6 mm.

[0106] In this example, the non-circular, opaque region shown is an omitted area within a 6mm diameter circle tangent to a transparent region defined as a regularly shaped star. In this example, the area of ​​the transparent region within the optical region defined by the regularly shaped star is approximately 23.32 square millimeters. In this example, the area of ​​the non-circular, opaque region is approximately 4.94 square millimeters.

[0107] Figure 11 Showing by Figure 10 One of the exemplary embodiments disclosed herein is the spectral characteristics of a retinal image formed on an illustrative myopic model eye as described in Table 1.

[0088] The single-vision contact lens described in the paragraph is configured in two different configurations, (a) without any expected non-circular, non-transparent features, and (b) having Figure 10 The expected non-circular, non-transparent aperture stop features described in (1003) are as follows.

[0108] When compared with the spectral characteristics of a retinal image (1101) obtained by a single-vision contact lens without any features of the present disclosure, the use of a non-circular, non-transparent aperture stop (1003) configured within the single-vision contact lens helps to redistribute light energy to the tilt frequencies of the spectral characteristics of the retinal image (1102), triggering a stop signal to the eye with progressive myopia.

[0109] In this example, the spectral characteristics represent 60% of the energy captured in the power spectral analyses (1101 and 1102) described herein. In other examples, additional power spectral analyses may be required to include at least 80% or 90% of the captured energy within the spectral characteristics.

[0110] In this example, using a transparent region with a regularly shaped star-shaped aperture may result in a non-circular, non-transparent region that is too narrow to be effective in all cases. Either too much light is blocked, or the natural pupil shape causes the aperture to overshadow the disclosed feature. Both are undesirable situations, in which case the design feature can be optimized to address the problem of variable pupil size due to varying lighting conditions that the wearer may experience in daily life. For example, one method of optimizing the design feature may include separating and reconfiguring six smaller triangles (1003a to 1003f) of the regularly shaped star-shaped aperture at different distances from the center. At least one edge will affect the power spectrum of the spectral characteristics of the retinal image while maintaining some desired modulation of the luminous flux. Alternatively, in some other embodiments of this disclosure, such optimization of the design feature may also include making the proposed regularly shaped star-shaped aperture off-center with irregular features. A modified non-circular, non-transparent aperture stop feature (1003) configured within the contact lens can be considered, such that energy is distributed to the tilt frequencies of the spectral characteristics of the on-axis and / or off-axis retinal image. This is to trigger a stop signal for progressive myopia. Various other physiological factors of myopia can also be incorporated into the optimization of design features, thereby achieving an overall balance between maintaining stimulation to slow progressive myopia and the visual performance of the contact lens.

[0111] In this example, the following parameters were used for calculation: (a) the pupil diameter on the model eye was 6 mm; (b) a polychromatic wavelength source representing the photometric function; (c) a field of view of 20 degrees; and (d) Figure 5 The outdoor artificial scene (502) described in the document.

[0112] Example 4

[0113] Figure 12 A front view of an exemplary contact lens embodiment is shown, not drawn to scale. The front view shows the optical region (1201), the lens diameter (1202), and a design feature (1203) namely the non-circular, non-transparent feature of the aperture stop. In this example, the lens diameter is approximately 14 mm, and the optical region is designed to be substantially single-vision refractive and has a diameter of approximately 6 mm.

[0114] In this example, the characteristic non-circular opaque region is an omitted area within a circle with a diameter of 6 mm inscribed in the regular-shaped Maltese cross. In this example, the area of ​​the transparent region within the optical region defined by the regular shape is approximately 24 square millimeters. In this example, the area of ​​the non-circular opaque region is approximately 4 square millimeters.

[0115] Figure 13 Showing by Figure 12 One of the exemplary embodiments disclosed herein is the spectral characteristics of a retinal image formed on an illustrative myopic model eye as described in Table 1.

[0088] The single-vision contact lens described in the paragraph is configured in two different configurations, (a) without any expected non-circular, non-transparent features, and (b) having Figure 12 The expected non-circular, non-transparent aperture stop features described in (1203) are as follows.

[0116] When compared with the spectral characteristics of a retinal image (1301) obtained by a single-vision contact lens without any features of the present disclosure, the use of a non-circular, non-transparent aperture stop (1203) configured within the single-vision contact lens helps to redistribute light energy to the tilt frequencies of the spectral characteristics of the retinal image (1302), triggering a stop signal to the eye with progressive myopia.

[0117] In this example, the spectral characteristics represent 60% of the energy captured in the power spectral analyses (1301 and 1302) described herein. In other examples, additional power spectral analyses may be required to include at least 80% or 90% of the captured energy within the spectral characteristics.

[0118] In this example, the following parameters were used for calculation: (a) a pupil diameter of 6 mm on the model eye; (b) a monochromatic wavelength source of 0.589 μm; (c) a field of view of 25 degrees; and (d) Figure 5The outdoor artificial scene (502) described in the document.

[0119] In another embodiment of the contact lens, the optical region may have an astigmatic design to correct the wearer's distance-related refractive errors. In yet another embodiment, the optical region may have an aspherical design, i.e., incorporating spherical aberration (positive or negative). In still another embodiment, the non-circular, non-transparent aperture may be elliptical, triangular, square, rectangular, pentagonal, hexagonal, heptagonal, octagonal, star-shaped, or other types of polygons.

[0120] In another contact lens embodiment, the design feature, namely the non-circular, non-transparent aperture stop, may be contained within 1, 2, 3, 4, 5, or 6 millimeters of the center of the contact lens's optical area. In yet another contact lens embodiment, the design feature, namely the non-circular, non-transparent aperture stop, may be contained between 1 and 3 millimeters, or between 2 and 4 millimeters, or between 3 and 5 millimeters, or between 2 and 6 millimeters of the center of the contact lens's optical area. The choice of the size of the non-circular, non-transparent aperture stop may take into account the maximum and minimum variations in the physiological size of the pupil. In some other contact lens embodiments, the intended design feature of the contact lens may be located, formed, or placed on one of the two surfaces of the contact lens, and the other surface may have additional features for further reducing eye growth. For example, using other features such as defocus, astigmatism, or spherical aberration. To avoid insufficient transmittance entering the wearer's eye, the size of the non-circular, non-transparent aperture is chosen such that the total transmittance through the intended lens is at least 85%, 90%, or 95% of that of standard single-vision lenses of the prior art.

[0121] In some embodiments of this disclosure, a non-circular, non-transparent aperture stop can be used to configure the stop signal; otherwise, it is designed with single-vision optics without significant spherical aberration. In other embodiments, the optical region of soft or rigid contact lenses can be designed with single-vision optics having positive or negative spherical aberration. In still other embodiments, the optical region of soft or rigid contact lenses can be additionally designed with single-vision optics, which includes spherical and cylindrical refractive power to correct the wearer's distance refractive error.

[0122] Figure 14A rigid gas-permeable orthokeratology contact lens embodying the principles of this disclosure is shown. When the lens of this disclosure is positioned on the cornea of ​​a myopic eye and configured to have ocular support regions in the central cornea (1411) and other selected areas of the cornea (1412, 1413), uniform pressure on the lens can be confirmed when the eyelids (not shown) are closed, thereby enabling corneal reshaping. Based on the corneal surface topography of the myopic eye (1411, 1412, and 1413), a selective arrangement of the curvature of the posterior surface (1401, 1402, and 1403) of the lens defines the ocular support regions, thereby allowing reshaping of the corresponding portion of the myopic cornea. According to one of the embodiments of this disclosure, such as Figure 14 As shown, a rigid gas-permeable contact lens for orthokeratology of myopia includes at least three regions: a base curve region (1401), at least one calibration curve region (1402), and a peripheral curve region (1403); the base curve region is disposed on a non-circular region that spans the defined region, the curvature of which is less than the measured curvature of the central corneal region (1411), and generates principal pressure to flatten the central corneal region and provide myopia correction for that region. A calibration arc region (1402) surrounds or circums the base arc region and is configured to have a larger shape, size, and curvature than the base arc region (1401) to generate secondary pressure to flatten the central corneal region; and at least one peripheral arc region (1403) surrounding the calibration arc region (1402) is configured to have a further defined shape, size, and curvature smaller than the curvature (1413) of the mid-peripheral portion of the measured cornea, so that the lens is substantially aligned and centered above and in the central corneal region; wherein, when the lens is worn on a myopic eye, the non-circular base arc region (1401) of the lens produces a corresponding flattened non-circular corneal region (1411) as a non-circular aperture; wherein light entering the myopic eye through the non-circular aperture introduces an additional, at least partial, diffraction effect, causing a portion of the light energy to be distributed in a tilted direction on the retina, and the signal observed in the spectral characteristics at the tilted frequency, simulating the visual experience of a visualized natural scene, thereby generating a stop signal for progressive myopia. In this example, the spectral characteristics represent 60% of the energy captured in the power spectrum analysis described herein.

[0123] A rigid gas-permeable orthokeratology lens for myopia includes: a base curve portion configured to have a curvature flatter than the central corneal region of the myopic eye; and a fitting curve portion having a curvature much greater than the base curve curvature. The calibration curve portion of the lens has a curvature steeper than the lower portion of the cornea, allowing it to contact the corneal portion. When the lens is fitted to the eye, the calibration, fitting, and base curve portions combine to provide pressure to the central corneal region, thereby flattening the central portion of the cornea and achieving sufficient refractive correction with the eyelids closed. The peripheral curve portion of the lens has a curvature flatter than the cornea. The radial intersection point of the base curve and fitting curve portions differs for different azimuth angles, resulting in a non-circular flat region on the cornea. This non-circular flat region creates a non-circular effective pupil positioned at an angle of inclination, artificially introducing energy distribution along the inclination direction in the spectral characteristics, thereby generating a stop signal for progressive myopia. In some embodiments, at least one peripheral arc region is designed to include a thickness characteristic that provides robust stability of the lens under eye closure conditions. This invention can be used in conjunction with any device / method that can potentially influence the development of myopia. These may include, but are not limited to, various designs of spectacle lenses, tint filters, pharmaceutical formulations, behavioral changes, and environmental conditions that may be considered by those skilled in the art. Few other exemplary embodiments are described in the following set of examples.

[0124] Example set "A"

[0125] A contact lens for slowing, delaying, or preventing one of the progressions of myopia, comprising an optical zone and a non-optical zone having an optical center; the optical zone comprising: a transparent region having a substantially single-light distribution configured to substantially match the refractive error of the myopic eye, thereby providing a focused retinal image of an incident light beam entering the myopic eye; wherein spectral features are generated when the retinal image is characterized using a power spectrum of Fourier transform; and a non-circular, non-transparent region surrounding the transparent region, configured to form an aperture stop of the contact lens; wherein the aperture stop of the contact lens is capable of at least partially redistributing the incident light to a plurality of tilted spatial frequencies of the spectral features, such that the redistributed spectral image simulates the spectral features of a natural scene. The redistributed spectral image provides an optical stopping signal to slow the progression of myopia.

[0126] The contact lens of one or more of the preceding claims in Example Set A, wherein the area of ​​the transparent region is at least 12.5 square millimeters, 15 square millimeters, 17.5 square millimeters, 20 square millimeters, 22.5 square millimeters, or 25 square millimeters.

[0127] The contact lens of one or more of the preceding claims in Example Set A, wherein the area of ​​the non-circular, non-transparent region is at least 2.5 square millimeters, 5 square millimeters, 7.5 square millimeters, 10 square millimeters, or 12.5 square millimeters.

[0128] The contact lens of one or more of the preceding claims in Example Set A, wherein the shape of the non-circular, non-transparent region is substantially like a regular polygon, between 3 and 12 sides, between 5 and 12 sides, between 5 and 8 sides, between 5 and 10 sides, or between 6 and 14 sides.

[0129] Example set A of one or more of the preceding claims of contact lenses, wherein the shape of the non-circular, non-transparent region is substantially unlike that of a rectangle, square, or rhombus.

[0130] The contact lens of one or more of the preceding claims in Example Set A, wherein the non-circular non-transparent region is translucent, partially opaque, or substantially opaque.

[0131] Example set A: contact lenses of one or more of the preceding claims, wherein the non-circular, non-transparent region is configured such that its diameter is substantially larger than the physiological pupil of a myopic eye, as measured under dark or dim lighting conditions.

[0132] Example set A: One or more contact lenses according to the preceding claims, wherein the transparent area includes spherical and astigmatic regions.

[0133] The contact lens of one or more of the preceding claims in Example Set A, wherein the transparent region includes positive or negative spherical aberration.

[0134] Example set A: contact lenses of one or more of the preceding claims, wherein the non-circular, non-transparent region is substantially off-center relative to the optical center of the contact lens.

[0135] The contact lens of one or more of the preceding claims in example set A, wherein the natural scene includes a forest scene, a mountain scene, a field scene, a beach scene, a coast scene, a river scene, or a waterfall scene.

[0136] Example set A includes one or more contact lenses according to the preceding claims, wherein the redistributed spectral image is substantially different from the spectral characteristics of the artificial scene.

[0137] The contact lens of one or more of the preceding claims in example set A, wherein the artificial scene includes an indoor scene, a street scene, a high-rise building scene, a cityscape scene, a highway scene, an office scene, or a portrait scene.

[0138] Example set A includes one or more of the preceding claims of contact lenses, wherein the contact lenses provide the wearer with sufficient field of vision, which is substantially no different from conventional or traditional single-vision contact lenses without non-circular, non-transparent areas.

[0139] Example set A includes one or more of the preceding claims of contact lenses, wherein the contact lenses provide sufficient visual performance to the wearer that is substantially no different from conventional or traditional single-vision contact lenses without non-circular, non-transparent areas.

[0140] Example set A includes one or more of the preceding claims of a contact lens, wherein the lens is capable of providing visible light transmittance within 80% of the visible light transmittance provided by a conventional or traditional single-vision contact lens without non-circular, non-transparent areas.

[0141] The contact lens of one or more of the preceding claims in Example Set A, wherein the calculation of the simulated retinal image resulting in spectral characteristics includes a pupil diameter between 3 mm (inclusive) and 6 mm (inclusive).

[0142] The contact lens of one or more of the preceding claims in Example Set A, wherein the calculation of the simulated retinal image resulting in spectral characteristics includes visible light wavelengths between 460 nm and 760 nm.

[0143] The contact lens of one or more of the preceding claims in Example Set A, wherein the calculation of the simulated retinal image results in spectral features including a field of view of at least 5 degrees, 10 degrees, 15 degrees, 20 degrees, 25 degrees, or 30 degrees.

[0144] The contact lens of one or more of the preceding claims in Example Set A, tested on a model eye with distance-related refractive errors configured to match a basic refractive characteristic curve, provides a retinal image for a pupil between 3 mm (inclusive) and 6 mm (inclusive), and at least one wavelength between 420 nm (inclusive) and 760 nm (inclusive); wherein the retinal image characterized by a Fast Fourier Transform produces spectral features. The aperture stop of the contact lens redistributes the incident light to multiple tilted spatial frequencies of the spectral features, such that the redistributed spectral image simulates the spectral features of a natural scene. The redistributed spectral features are substantially different from those obtained by conventional or traditional single-vision contact lenses without non-circular, non-transparent regions when tested on a model under similar conditions.

[0145] The contact lens of one or more of the preceding claims in Example Set A, wherein the model eye is a schematic, physical, or desktop model eye.

[0146] Example set A: One or more contact lenses according to the preceding claims, wherein the non-circular, non-transparent aperture of the lens generates a stop signal for radially progressive myopia.

[0147] Example set "B"

[0148] An orthokeratology contact lens for myopia includes at least three regions: a base curve region, a calibration region, and at least one peripheral arc region; the base curve region is configured on a non-circular region spanning a defined region, the curvature of which is less than the curvature measured in the central corneal region, and generates initial pressure to flatten the central corneal region and provide correction for myopia; the calibration region surrounding the non-circular base curve region is configured with a shape, size, and curvature greater than that of the base curve region, generating secondary pressure to flatten the central corneal region; at least one peripheral arc region surrounding the calibration region is configured with a defined shape, size, and curvature less than the curvature of the intermediate peripheral portion of the cornea, so that the lens is substantially aligned and centered in the central corneal region; wherein, when the lens is placed in the myopic eye, the non-circular base curve region of the lens generates a corresponding flattened non-circular corneal region as a non-circular aperture; wherein light entering the myopic eye through the non-circular aperture introduces an additional diffraction effect, causing a portion of the light energy to be allocated as tilted frequencies in the spectral characteristics of the retinal image.

[0149] The lens of the aforementioned example in example set B, wherein the lens is made of a breathable material.

[0150] One or more of the lenses in Example Set B of the foregoing examples, wherein the measured central corneal region spans a diameter of at least 2 millimeters.

[0151] One or more of the lenses in Example Set B of the foregoing examples, wherein the diameter of the measured central corneal region is at least 3 millimeters.

[0152] One or more lenses of the foregoing examples in Example Set B, wherein the curvature of the base curve region of the lens is at least 0.5D, or 0.75D, or 1D flatter than the measured central corneal region.

[0153] One or more lenses of the foregoing examples in Example Set B, wherein the area of ​​the base curve region of the lens is at least 15 square millimeters, 18 square millimeters, or 21 square millimeters.

[0154] One or more of the lenses in Example Set B of the foregoing examples, wherein the non-circular shape of the base arc region of the lens may be elliptical, triangular, square, rectangular, pentagonal, hexagonal, heptagonal, octagonal, star-shaped or another type of polygon.

[0155] Lenses of one or more of the aforementioned examples in Example Set B, wherein the boundary line defining the polygonal shape of the non-circular, non-transparent aperture can be curved or pincushion-shaped.

[0156] One or more lenses of the foregoing examples in Example Set B, wherein the curvature of the calibration arc region of the lens is at least 0.5D, 0.75D, or 1D steeper than the curvature of the base arc region.

[0157] One or more lenses of the foregoing examples in Example Set B, wherein the area of ​​the calibration arc region of the lens is at least 9 square millimeters, 12 square millimeters, or 15 square millimeters.

[0158] One or more lenses of the foregoing examples in Example Set B, wherein the shape of the calibration arc region of the lens may be non-circular or elliptical.

[0159] One or more lenses of the aforementioned examples in Example Set B, wherein the number of peripheral arc regions on the lens may be one, two or three regions.

[0160] One or more lenses of the aforementioned examples in Example Set B, wherein the peripheral portion of the measured corneal region spans a width of at least 2 millimeters.

[0161] One or more lenses of the foregoing examples in Example Set B, wherein the curvature of at least one peripheral arc region of the lens is at least 0.25D flatter than the measured curvature of its mid-peripheral portion of the cornea.

[0162] One or more lenses of the foregoing examples in Example Set B, wherein the curvature of at least one peripheral arc region of the lens is at least 0.5D, 0.75D, or 1D flatter than the curvature measured in the mid-peripheral portion of the cornea.

[0163] One or more lenses of the foregoing examples in Example Set B, wherein the area of ​​at least one peripheral arc region of the lens is at least 3 square millimeters, 6 square millimeters, or 9 square millimeters.

[0164] One or more lenses of the foregoing examples in Example Set B, wherein at least one peripheral arc region of the lens may be circular or elliptical in shape.

[0165] One or more lenses of the aforementioned examples in Example Set B, wherein at least one peripheral arc region of the lens includes a thickness profile that provides robust stability of the lens under eye closure conditions.

[0166] One or more of the lenses in Example Set B of the foregoing examples, wherein the non-circular quasi-aperture of the lens is capable of modifying the incident light so that the retinal image characteristics simulate the spectral features of an image formed in a visualized natural scene.

[0167] One or more lenses of the aforementioned examples in Example Set B, wherein the non-circular aperture of the lens generates a stop signal to the progressive myopia.

[0168] A method for reducing the progression of myopia in a person by providing at least one lens, as described in one or more of the foregoing examples in Example Set B.

Claims

1. A contact lens for myopia, the contact lens comprising an optical region having an optical center and a non-optical peripheral region; the optical region comprising: A transparent region exhibiting single-light characteristics; A non-circular, non-transparent region surrounding the transparent area is configured to form the aperture stop of the contact lens; The contact lens was characterized by testing on a model eye with distance refractive error configured to match the single-vision refractive power, providing a retinal image with at least one pupil diameter between 3 mm and 6 mm, at least one wavelength between 420 nm and 760 nm, and at least one wide field of view over the retina; Among these, when spectral Fourier transform analysis is used to further characterize retinal images, the spectral characteristics of the retinal images are generated; The aperture stop of the contact lens can at least partially redistribute the incident light energy entering the model eye to multiple tilted spatial frequencies of the spectral characteristics; The spectral characteristics differ from those obtained under similar conditions when testing the single-light distribution characteristics of a single-light contact lens configured with an apertureless aperture on the model eye; and The spectral characteristics of retinal images differ from those obtained through power spectrum Fourier transform analysis of man-made scenes; these man-made scenes include indoor scenes, street scenes, high-rise building scenes, urban scenes, highway scenes, office scenes, or portrait scenes. The transparent area described herein spans an area of ​​at least 12.5 square millimeters.

2. The contact lens according to claim 1, wherein, The model eye is schematic, physical, or desktop model eye.

3. The contact lens of claim 1, wherein the non-circular, non-transparent region spans an area of ​​at least 2.5 square millimeters.

4. The contact lens according to claim 1, wherein the shape of the non-circular, non-transparent region is a regular polygon with more than 3 sides and no more than 12 sides.

5. The contact lens according to claim 1, wherein the shape of the non-circular, non-transparent area is not rectangular, square, or rhomboid.

6. The contact lens according to claim 1, wherein, The transparent area includes a spherical surface and / or astigmatism.

7. The contact lens according to claim 1, wherein, The transparent area includes positive or negative spherical aberration.

8. The contact lens according to claim 1, wherein the non-circular non-transparent region is translucent, partially opaque, or opaque.

9. The contact lens of claim 1, wherein the non-circular, non-transparent region is off-center relative to the optical center of the contact lens.

10. The contact lens according to claim 1, wherein, The non-circular, non-transparent region is configured such that its diameter is significantly larger than the physiological pupil of a myopic eye as measured under dark field or low light conditions.

11. The contact lens according to claim 1, wherein, The spectral features of the retinal image are modeled after the spectral features obtained by power spectrum Fourier transform analysis of natural scenes; wherein, natural scenes include forest scenes, mountain scenes, field scenes, beach scenes, coastal scenes, river scenes, or waterfall scenes.

12. The contact lens according to claim 1, wherein, The spectral characteristics of the retinal image provide an optical stopping signal to slow the progression of myopia.

13. The contact lens of claim 1, wherein the contact lens provides the wearer with a sufficient field of vision that is indistinguishable from that of a conventional single-vision contact lens without the non-circular, non-transparent aperture stop.

14. The contact lens of claim 1, wherein the contact lens provides sufficient visual performance to the wearer, said visual performance being indistinguishable from that of a conventional single-vision contact lens without said non-circular, non-transparent aperture stop.

15. The contact lens according to claim 1, wherein, The visible light transmittance that a contact lens can provide is at least 80% of that provided by a conventional single-vision contact lens without a non-circular, non-transparent aperture diaphragm design.

16. The contact lens according to claim 1, wherein, The retinal image that results in spectral characteristics includes at least two pupil diameters between 3 mm and 6 mm.

17. The contact lens according to claim 1, wherein, A retinal image that results in spectral characteristics includes at least two visible light wavelengths between 460 nm and 760 nm.

18. The contact lens according to claim 1, wherein, The wide field of view of a retinal image that results in spectral characteristics includes at least 15 degrees.

19. The contact lens of claim 1, wherein the spectral characteristics represent at least 60% of the energy captured within the power spectrum Fourier transform analysis.

Images