Ophthalmic lenses for the eyes

Abstract

This application relates to ophthalmic lenses for use in the eye. The ophthalmic lens includes an anterior surface, a posterior surface, an optical center, and an optical region surrounding the optical center. The optical region includes a basic prescription for the eye and multiple non-refractive features; wherein the basic prescription includes spherical correction, astigmatism correction, or spherical and astigmatism correction. The non-refractive features contribute to increased retinal ganglion cell activity in the wearer, which can serve as an optical stopping signal to slow, improve, control, inhibit, or reduce the rate of myopia progression in the wearer.

Description

[0001] This application is a divisional application of the invention patent application filed on November 30, 2020, with application number 202080094716.6 (PCT / AU2020 / 051296) and entitled "Design of an ophthalmic lens with non-refractive features". Cross-references to related applications

[0002] This patent application claims priority to Australian Provisional Application No. 2019 / 904536 entitled “A multi-zone ophthalmiclens”, filed on 1 December 2019, and another Australian Provisional Application No. 2019 / 904537 entitled “An Ophthalmic lens for myopia”, filed on 1 December 2019, the entire contents of which are incorporated herein by reference. Technical Field

[0003] This disclosure relates to ophthalmic lenses, particularly contact lenses and spectacle lenses, for use with eyes suffering from conditions related to axial length, such as myopia. Background Technology

[0004] The human retina has three main layers: the photoreceptor layer, the outer plexiform layer, and the inner plexiform layer. Cones and rods are photoreceptors in the retina that respond to light by converting incident light into electrical signals. These converted electrical signals travel from the photoreceptors through bipolar cells to the retinal ganglion cells and optic nerve, transmitting visual information from the retinal cells to the brain, allowing for visual perception of the world. Photoreceptors respond with tiered membrane potentials and release the neurotransmitter glutamate in proportion to their polarization state. For example, in the absence of light stimulation, photoreceptors depolarize and release more glutamate relative to their baseline state. In the presence of light, hyperpolarization of the photoreceptors, due to the breakdown of opsins within the photoreceptors, causes them to release less glutamate relative to their baseline state. There are two types of bipolar cells in the retina: light-giving bipolar cells and light-removing bipolar cells. Light-giving bipolar cells and light-removing bipolar cells encode the positive and negative spatiotemporal contrast of incident light, respectively, by comparing photoreceptor signals with spatiotemporal averages calculated by the lateral connecting layer of horizontal cells.

[0005] Horizontal cells are interconnected via conductive gap junctions, and these horizontal cells connect to bipolar cells and photoreceptors in a complex triplet synapse. Photosensitive and photodesensitive bipolar cells respond differently to glutamate based on the type and number of glutamate receptors located on each of these bipolar cells.

[0006] Central bipolar cells in the light-deprivation region possess ion channel receptors that are excitatory to glutamate. These cells depolarize in response to glutamate while retaining the signal from the photoreceptor. In the presence of light, these cells receive less glutamate from the photoreceptor, leading to hyperpolarization and the release of less glutamate to the corresponding downstream ganglion cells. In the absence of light, they receive more glutamate from the photoreceptor, leading to depolarization and the release of more glutamate to the corresponding downstream ganglion cells.

[0007] Photoreceptor bipolar cells possess metabolic receptors that inhibit glutamate. These photoreceptor bipolar cells hyperpolarize in response to glutamate, reversing the sign of the photoreceptor signal. In the presence of light, photoreceptor bipolar cells receive less glutamate from the photoreceptors, leading to depolarization and the release of more glutamate to the corresponding downstream ganglion cells. In the absence of light, photoreceptor bipolar cells receive more glutamate from the photoreceptors, leading to hyperpolarization and the release of less glutamate to the corresponding downstream ganglion cells. The more glutamate released by either photoreceptor or depolaror bipolar cells to the corresponding downstream ganglion cells, the larger the action potential of the ganglion cells. The opposite response to light between photoreceptor and depolaror bipolar cells is key to the different responses in bright and dark states. Furthermore, the depolarization signaling activity of photoreceptor and depolaror bipolar cells can be amplified or inhibited by horizontal cells connected to peripheral photoreceptors in the corresponding receptive fields.

[0008] Horizontal cells receive excitatory input from photoreceptors and send inhibitory feedback back to photoreceptors connected in their surrounding neighborhood. The receptive field is a group of photoreceptors that transmit input downstream to bipolar cells and ganglion cells in the retina.

[0009] The retinal receptive field can be described using concentric circular regions: these regions have a small central circular field and a wider annular field surrounding the central field, known as the peripheral field. Receptive fields are classified into two types: light-deprivation-central and light-on-periphery receptive fields, and light-on-central and light-deprivation-periphery receptive fields. The light-on-central and light-deprivation-central receptive fields are based on the different responses to light produced by bipolar cells.

[0010] Humans are born farsighted, meaning their eyeballs are too short for their total optical power. As a person grows from childhood to adulthood, the eyeball continues to grow until the eye's refractive state stabilizes. Eye growth is understood to be controlled by feedback mechanisms and primarily regulated by visual experience to match the eye's optics with its length and maintain homeostasis. This process is called emmetropization. The signals that guide the emmetropization process are initiated by modulating the light energy received by the retina. Retinal image features are monitored by biological processes that modulate these signals to start or stop, accelerate or slow eye growth. This process coordinates optics with eyeball length to achieve or maintain emmetropia. Derailment from this emmetropization process can lead to refractive disorders, such as myopia. It is hypothesized that reduced retinal activity promotes eye growth, and conversely, increased retinal activity inhibits eye growth.

[0011] In many parts of the world, particularly in East Asia, the prevalence of myopia is increasing at an alarming rate. In myopic individuals, the axial length of the eye is mismatched with the overall focal length of the eye, causing distant objects to focus in front of the retina.

[0012] A simple negative monocular lens can correct myopia. While such devices can optically correct refractive errors associated with axial length, they do not address the underlying cause of excessive eye growth in the progression of myopia. Excessive axial length in high myopia is associated with serious vision-threatening conditions such as cataracts, glaucoma, myopic macular degeneration, and retinal detachment. Therefore, specific optical devices are still needed for such individuals that not only correct underlying refractive errors but also prevent excessive axial elongation or the progression of myopia. Summary of the Invention

[0013] definition

[0014] Unless otherwise specified below, the terminology used herein is the same as that commonly used by those skilled in the art.

[0015] The term "myopic eye" means an eye that has experienced myopia, is in the pre-myopic stage, is at risk of developing myopia, or has been diagnosed with a refractive condition that is progressing toward myopia with or without astigmatism.

[0016] The term “progressive myopic eye” refers to an eye that has been diagnosed with progressive myopia, measured as a change in refractive error of at least -0.25 D / year or a change in axial length of at least 0.1 mm / year.

[0017] The term “eye at risk of developing myopia” refers to an eye that may be normal or slightly hyperopic at the time, but has been identified as having an increased risk of developing myopia based on genetic factors (e.g., both parents are myopic) and / or age (e.g., slightly 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).

[0018] The term "optical stop signal" or "stop signal" refers to an optical signal or directional cue that can help slow down, reverse, stop, delay, inhibit, or control the growth of the eye and / or the refractive condition of the eye.

[0019] The terms "spatial and temporally varying optical stop signal" or "spatial and temporally changing optical stop signal" refer to an optical stop signal provided at the retina that changes over time and spatially across the retina of the eye.

[0020] The term "contact lens" refers to a finished contact lens that is designed to fit onto the wearer's cornea to affect the optical performance of the eye.

[0021] The term "spectacle lens" can refer to a finished or semi-finished blank lens. The terms "standard single-vision lens," "commercially available single-vision lens," or "standard glasses" refer to a spectacle lens with a basic prescription for correcting underlying refractive errors in the eye; wherein the refractive error can be myopia with or without astigmatism.

[0022] The term "optical zone" or "light zone" refers to the area on an ophthalmic lens (such as a contact lens or spectacle lens) that contributes to the prescription optical effect. The optical zone includes one or both of the front and rear optical zones. The front and rear optical zones refer to the front and rear surface areas of the contact lens, respectively, each contributing to the prescription optical effect.

[0023] The term "optical center" or "visual center" refers to the geometric center of the optical zone of an ophthalmic lens. The terms "geometric" and "geometric" are essentially the same.

[0024] The term "optical axis" refers to a line that passes through the optical center and is substantially perpendicular to the plane containing the edge of the ophthalmic lens.

[0025] The terms or phrases “single-view optical zone” or “essentially single-view optics” or “essentially single-view profile” or “spherical optical zone” refer to an optical zone with a uniform power distribution and without significant principal spherical aberrations. The single-view optical zone can also be further classified to include astigmatic components to correct distance refractive errors.

[0026] The term "model eye" can refer to intentional, ray-traced, or physical model eyes.

[0027] As used herein, the terms “diopter,” “focal power,” or “D” are units of measurement for refractive power, defined as the reciprocal of the focal length (in meters) of a lens or optical system along its optical axis.

[0028] A detailed discussion of the prior art and the subject matter of general concern is provided as background to this disclosure, to illustrate the context of the disclosed embodiments, and further, to distinguish the advancements contemplated by this disclosure relative to the prior art. Based on the priority of the various embodiments and / or claims set forth in this disclosure, the material presented herein should not be construed as an admission that the material referenced is part of previously disclosed, known, or common general knowledge.

[0029] In brief, all prior art optical designs with refractive or phase-change features for managing myopia involve significant visual impairment, primarily due to the use of similar multifocal design features commonly considered in the art. Examples are described in U.S. Patents 6,045,578, 7,025,460, 7,506,983, 7,401,922, 7,803,153, 8,690,319, 8,931,897, 8,950,860, and 8,998,408.

[0030] In the field of optics, a series of solutions have been proposed to improve the focusing depth for general imaging systems by changing amplitude characteristics. Examples are described in the following: the paper entitled "Improvement in the OTF of a defocused optical system through the use of shaded apertures" by Mino and Okano, published in Applied Optics 1971; the paper entitled "Arbitrary high focal depth with a quasi-optimum real and positive transmittance apodizer" by Castaneda et al., published in Applied Optics 1989; the paper entitled "Zone plate for arbitrary high focal depth" by Castaneda and Berriel-Valdos, published in Applied Optics 1990; and U.S. Patents 5,965,330A, 8,570,655B2, and 8,192,022.

[0031] The disadvantages of using amplitude-changing solutions include reduced energy transfer at the critical frequency, poorer resolution compared to phase-changing solutions, and low luminous flux.

[0032] In contrast, this disclosure relates to the use of a single-vision ophthalmic lens design with a plurality of non-refractive features intentionally configured to provide an increase in retinal ganglion cell activity and overcome one or more of the disadvantages of the prior art as described herein.

[0033] Some disclosed embodiments involve modifying incident light using a contact lens or spectacle lens that utilizes a stop signal to slow the rate of myopia progression. More specifically, this disclosure relates to the use of a single-vision contact lens and a single-vision spectacle lens for correcting a wearer's myopia, wherein the single-vision ophthalmic lens device is configured with a basic prescription for correcting an individual's myopia, and the single-vision ophthalmic lens device is also intentionally configured with a non-refractive feature that facilitates an increase in retinal ganglion cell activity in the wearer, which serves as an optical stop signal to inhibit, reduce, or control the rate of myopia progression in the wearer. In some embodiments, the optical stop signal may be configured to have spatiotemporal variation.

[0034] Some disclosed embodiments include contact lenses and / or spectacle lenses for altering the properties of incident light entering the human eye. Some disclosed embodiments relate to the configuration of contact lenses and / or spectacle lenses for correcting, managing, and treating refractive errors, such as myopia. Some embodiments are designed not only to correct myopic refractive errors but also to simultaneously provide an optical stop signal that prevents further eye growth or myopia progression.

[0035] Some embodiments relate to an instrument, device, and / or method capable of modifying incident light via an ophthalmic lens to provide an effective increase in retinal ganglion cell activity, thereby slowing the growth of an individual's eye. This can be accomplished by configuring a specific non-refractive feature for use in conjunction with a single-vision ophthalmic lens, the non-refractive feature being designed to introduce an artificial rim pattern or artificial luminous contrast profile applied to the central and / or peripheral retina. The artificial rim pattern or artificial luminous contrast profile applied to the retina provides a spatial contrast profile across the light-provided-central and light-removed-central retinal fields throughout the retina. The artificially induced rim provides an increase in retinal spike activity or ganglion cell excitation activity, which is a surrogate measure of overall retinal activity. The present disclosure presupposes that the increased retinal ganglion cell activity can, in turn, provide an optical stopping signal for progressive myopia in the eye.

[0036] In some other embodiments of this disclosure, the non-refractive features of the contact lens are configured such that the artificial edge pattern or artificial spatial luminescent contrast profile applied to the retina is further configured to provide temporal variations in overall retinal ganglion cell activity.

[0037] Certain embodiments of this disclosure relate to one or more variations of the structural characteristics of non-refractive features used in combination with the single-vision ophthalmic lenses disclosed herein—both contact lenses and spectacle lenses. For example, the structural characteristics of the non-refractive features include one or more of the following: the opacity of the non-refractive feature, the size, width, and shape of the non-refractive feature, the method of application of the non-refractive feature to the ophthalmic lens, the application location of the non-refractive feature to the ophthalmic lens, the distribution of the non-refractive feature to the ophthalmic lens, the arrangement pattern of the non-refractive feature to the ophthalmic lens, and the area it spans.

[0038] As disclosed herein, contemplated variations of many structural properties of non-refractive features provide desired functional visual performance on the eye while maintaining the effectiveness of ophthalmic lens implementations in slowing myopia progression. Certain embodiments of this disclosure relate to the optimization of non-refractive features to provide desired levels of increased retinal ganglion cell activity and / or desired levels of temporal variation without impairing the eye's resolving power; such optimizations include, but are not limited to, features such as: opacity, size, shape, variability, pattern, location, and application method. For example, in some embodiments of this disclosure, one or more non-refractive features are configured on an additional single-vision ophthalmic lens with a basic prescription to correct refractive errors in the eye. When tested on a model eye provided with multiple common visual scenarios—which may include environmental and / or behavioral scenarios considered associated with myopia development and / or progression—the ophthalmic lens provides an increase in retinal ganglion cell activity approximately 1.25 times, 1.5 times, 1.75 times, 2 times, 2.5 times, or 3 times that of a single-vision ophthalmic lens without non-refractive features. This retinal ganglion cell activity may include light-giving cells, light-reducing cells, or both within the receptive field. In some examples, retinal ganglion cell activity may be averaged over a local area, multiple local areas, or the entire desired retinal field. In some other embodiments, the ophthalmic lens tested on the model additionally provides temporal variations in retinal ganglion cell activity. In some examples, retinal ganglion cell activity can be measured by retinal spike sequence analysis, while in other examples, retinal ganglion cell activity can be measured by the average retinal spike rate as a function of time. In some other embodiments of this disclosure, when tested on a model eye, the ophthalmic lens of the embodiment provides an increased temporal variation, or fluctuation or oscillation, in retinal ganglion cell activity; wherein the temporal variation of retinal ganglion cell activity can be expressed as one or more of the following: non-monotonic fluctuations, quasi-sinusoidal variations, sinusoidal variations, periodic variations, non-periodic variations, non-periodic quasi-rectangular variations, rectangular variations, square wave variations, or random variations in retinal ganglion cell activity.

[0039] In some examples, specific types of visual stimuli can be used to induce retinal ganglion cell activity. These specific types of visual stimuli include, for example, white noise electrical stimulation, sinusoidal variations in visual stimuli, checkerboard patterns, full-field flash stimulation, half-field flash stimulation, full-field Gaussian noise, half-field Gaussian noise, regional flash stimulation, and regional Gaussian noise. In some implementations, only a coarse characterization of the neural response to the stimulus may be required; in other examples, a more refined characterization of the neural response to the stimulus may be necessary. The stimuli used in this disclosure are considered merely as representative methods to demonstrate the working principle of this disclosure, and this selection should not be construed as limiting the scope of this disclosure and / or the claims.

[0040] In some embodiments of this disclosure, the opacity of the non-refractive feature on the ophthalmic lens can be configured such that the feature absorbs at least 80%, at least 85%, at least 90%, at least 95%, at least 98%, at least 99%, or all 100% of the light incident on the non-refractive feature. In some other embodiments of this disclosure, the opacity of the non-refractive feature on the ophthalmic lens can be configured such that the feature absorbs between 80% and 90%, or between 80% and 95%, or between 80% and 99% of the light incident on the non-refractive feature.

[0041] In some embodiments of this disclosure, the width of any one or more elements of any single element of any non-refractive feature in the non-refractive feature may be configured such that the feature is at least 3 times, at least 4 times, at least 5 times, at least 6 times, at least 7 times, at least 8 times, at least 9 times, or at least 10 times the average wavelength of light in the visible spectrum (i.e., 555 nm).

[0042] In some embodiments of this disclosure, the width of any individual element of any non-refractive feature can be configured such that the width of the feature is between 3 and 5 times, or 4 and 7 times, or 5 and 9 times, or 3 and 10 times the average wavelength of light in the visible spectrum (i.e., 555 nm). Choosing the width of any individual element of the non-refractive feature to be significantly greater than the lower limit of the average wavelength of light in the visible spectrum is supported by the desired result of avoiding undesirable diffraction effects at the edges of the non-refractive features disclosed herein.

[0043] In some embodiments, the width of any one or more individual elements of the non-refractive feature on the ophthalmic lens can be configured such that the feature is no greater than 50 μm, or no greater than 75 μm, or no greater than 100 μm, or no greater than 150 μm, or no greater than 200 μm, or no greater than 250 μm, or no greater than 300 μm. The upper limit for the selection of the width / size of any individual element of the non-refractive feature is supported by the desired result of maintaining sufficient light entering the eye, which allows for minimal energy loss and thereby allows for substantially no alteration to the resolving power of the eye wearing the contemplated embodiments disclosed herein. In some embodiments, the upper limit for the selection of the width / size of any individual element of the non-refractive feature may differ between contact lens and spectacle lens embodiments, taking into account the fixed-point distance of the spectacle lens embodiment.

[0044] In some other embodiments of this disclosure, the non-refractive features can be tailored based on the degree and rate of myopia progression such that the effectiveness of reducing the rate of progression can be balanced with the required compromise in visual performance acceptable to the wearer.

[0045] In some embodiments of this disclosure, the shape of any one or more individual elements of a non-refractive feature that can be configured on an ophthalmic lens can be configured such that the feature is a circle, hexagon, octagon, regular polygon, irregular polygon, line, triangle, dot, arc, or any other random shape disclosed herein.

[0046] In some other embodiments, the shape of the envisioned design feature formed by multiple orifices, segments, regions or areas can be circular, non-circular, semi-circular, annular, elliptical, rectangular, octagonal, hexagonal or square.

[0047] In some embodiments of this disclosure, the arrangement of individual non-refractive features on a single-view contact lens can be configured such that the area spanned by all non-refractive features is within 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 4.5 mm, 5 mm, or 6 mm of the center diameter of the optical region of the single-view contact lens.

[0048] In some embodiments of this disclosure, the arrangement of individual non-refractive features on a single-vision lens can be configured such that the area spanned by all non-refractive features is within 20 mm, or 25 mm, or 30 mm, or 35 mm, or 40 mm, or 45 mm, or 50 mm, or 60 mm of the central diameter of the optical zone of the single-vision lens.

[0049] In some other embodiments of this disclosure, non-refractive features may be implemented in a region of 30%, 35%, 40%, 45%, 50%, 55%, or 60% of the center of the optical zone of a single-vision lens.

[0050] In some other embodiments of this disclosure, non-refractive features may be implemented in a 10%, 15%, 20%, 25%, 30%, 35%, or 40% peripheral area of ​​the optical zone of the single-vision lens. References to the central or peripheral portion of the single-vision lens are made from the optical center of the lens.

[0051] In some other examples of this disclosure, the non-refractive feature may be implemented at one or more of the following locations: the anterior surface of the ophthalmic lens, the posterior surface of the ophthalmic lens, and within the matrix of the ophthalmic lens material. In some embodiments, the non-refractive feature may be implemented via pad printing or laser printing methods as commonly used in the conventional development of cosmetic lenses.

[0052] In some embodiments of this disclosure, the non-refractive features achieved can be arranged substantially in the form of multiple apertures, multiple zones, multiple regions, and multiple segments on other generally single-vision ophthalmic lenses, which can promote an increase in retinal ganglion cell activity, as disclosed herein, which serves as an optical stop signal for suppressing, reducing, or controlling progressive myopic refractive errors.

[0053] In other embodiments, the non-refractive feature can be achieved via a homogeneous or non-homogeneous medium disposed in the substrate of the ophthalmic lens. In some other embodiments, this implementation may involve photolithography or other printing processes on the medium on the surface or within the substrate.

[0054] This disclosure relates to an ophthalmic lens that alters the transmission characteristics of incident light to produce a pronounced luminous contrast profile (i.e., an artificial edge) on the wearer's retina. The alteration of the eye's transmission characteristics is achieved by employing multiple relatively low-transmission lines or stripes, or alternatively by employing non-refractive features arranged as multiple apertures, sections, segments, regions, or other patterns contemplated herein. The low-transmission lines or stripes or features may be disposed on one or more locations on the ophthalmic lens: the anterior surface of the lens, the posterior surface of the lens, or the low-transmission lines or stripes or features may be embedded within the matrix of the ophthalmic lens. The low-transmission lines or stripes or features may be configured to be opaque, translucent, reflective, spectrally sensitive, polarization sensitive, or absorptive. To achieve polarization sensitivity, various combinations of linear polarization filters with or without quarter-wave plate retarders are contemplated. In some other embodiments, specific lens materials, such as birefringent materials, coatings, or combinations of birefringent materials and coatings, may be used to configure the desired polarization sensitivity.

[0055] The dimensions of low-transmission features, such as the width of non-refractive features, can be adjusted in the lens design as needed to increase the amount of light entering the eye, minimize visual artifacts, and adequately configure the ophthalmic lens to provide the wearer's eye with the required refractive correction and to maintain or provide sufficient stop signal for the wearer's eye.

[0056] Currently, the use of non-refractive features to slow the progression of myopia has been proposed. The use of non-refractive features facilitates implementations that do not employ positive defocus, positive spherical aberration, or any other variation, such as phase-changing methods with bifocal, multifocal, or extended depth of field in focusing optics.

[0057] A method for slowing the progression of myopia is currently proposed by introducing artificial edges or luminous contrast contours into the retinal image captured when viewed through an ophthalmic lens and providing an increase in retinal ganglion cell activity that may inhibit further eye growth.

[0058] In some embodiments, an optical lens may refer to a contact lens, while in other embodiments, an ophthalmic lens may refer to a spectacle lens. In some embodiments of this disclosure, the contemplated spectacle lens combined with non-contact features may result in an undesirable cosmetic appearance, which may be undesirable to the wearer. Additional material properties of the lens can be conceived to mitigate the problem of undesirable cosmetic effects. For example, in some embodiments, the achieved non-refractive feature may be configured to have one or more of the following additional material properties: completely insensitive, partially sensitive, or completely sensitive to the polarization state of incident light. In some other spectacle lens embodiments of this disclosure, the achieved non-refractive feature may be configured to be electrically adjustable. In some embodiments, a combination of pairs of polarized contact lenses and pairs of polarized spectacle lenses can be conceived to provide additional temporal variations in retinal ganglion cell activity without requiring excessive movement of the contact lens over the eye.

[0059] Some currently disclosed embodiments include contact lenses intentionally designed with non-refractive features, which are arranged, for example, in patterns such as wavy patterns, curved patterns, Memphis patterns, rectangular grid patterns, hexagonal patterns, spiral patterns, vortex patterns, radial patterns, a series of lines, zigzag patterns, or random patterns. These non-refractive features are configured within the optical zone to introduce a luminescent contrast profile, i.e., an artificial edge, in the retinal image. In one embodiment of this disclosure, the envisioned wavy pattern or wavy stripes can be achieved by generating a large-scale interference pattern when an opaque ridge pattern with transparent gaps is superimposed on another similar pattern that is laterally separated. In another embodiment, the wavy pattern can be achieved by printing ridge patterns on both surfaces of the contact lens with predetermined offsets and orientations. Alternatively, in other embodiments, the resulting wavy pattern can be printed or configured on one surface of the contact lens.

[0060] Some embodiments of this disclosure relate to a combined single-vision contact lens design made of hydrogel or silicone hydrogel materials, which incorporates non-refractive features within the optical zone of the single-vision contact lens to suppress, prevent, and / or control the progression of myopia.

[0061] Some ophthalmic lens embodiments of this disclosure provide spatiotemporal variations in the stop signal facilitated by ophthalmic lens movements, such as contact lenses, natural blinking of the eyelids when wearing contact lenses of this disclosure, or spatiotemporal variations in the stop signal caused by eye movements when wearing contemplated spectacle lens embodiments of this disclosure. The spatiotemporal variations in the presentation of the artificial edge profile or luminous contrast profile allow for a minimization of the saturation of effectiveness against the rate of myopia progression over time. The embodiments presented in this disclosure address the ongoing need for improved ophthalmic lenses that provide therapeutic benefits by inhibiting or reducing the rate of myopia progression while providing the wearer with visual performance equivalent to or sufficient for single vision across the entire range of distances and angles.

[0062] Certain other embodiments of this disclosure are designed to maintain the efficacy of the therapeutic benefits over time. Various aspects of the embodiments of this disclosure address such needs of the wearer. Embodiments of this disclosure relate to a contact lens for slowing, delaying, or preventing at least one of the progression of myopia. The contact lens includes an anterior surface, a posterior surface, an optical zone, and an optical center; wherein the optical zone surrounding the optical center is configured with a plurality of fine lines, or a plurality of stripes or fringes, and the optical zone is otherwise substantially configured with a single-vision prescription to at least partially provide sufficient foveal correction, and additionally, the contemplated design features are configured to at least partially provide an increase in retinal ganglion cell activity, thereby providing a stopping signal to reduce the rate of myopia progression.

[0063] According to some embodiments, the contact lens is configured with multiple non-refractive design features, such as multiple lines, stripes, apertures, or patterns, within a generally single-vision optical zone. These multiple non-refractive design features provide an effective increase in the retinal encoding of spatiotemporal signals facilitated by: supra-ocular movements of the contact lens, natural blinking of the eyelids, or eye movements while wearing the contact lens as envisioned herein. Therefore, the saturation of the effectiveness against the rate of myopia progression over time is minimized.

[0064] According to some embodiments, the spectacle lens is configured with multiple non-refractive features, such as multiple lines, stripes, apertures, or patterns, within a generally single-vision optical zone. These multiple non-refractive features provide an effective increase in retinal decoding of spatiotemporal signals facilitated by eye movements when wearing the spectacle lens contemplated herein. The embodiments presented in this disclosure address the ongoing need for improved optical designs for ophthalmic lenses that can suppress the progression of myopia while providing wearers with reasonable and sufficient visual performance for a range of activities that the wearer can undertake as part of their daily lives. Various aspects of the embodiments of this disclosure address these needs of the wearer. Exemplary methods of this disclosure include: measuring the refractive state of an individual's eye based on standard optometric techniques; determining a basic prescription for the eye based at least in part on the refractive measurements of the eye; selecting the power of the single-vision lens of this disclosure such that the power of the single-vision lens of this disclosure substantially matches the basic prescription required to correct potential refractive errors; and further selecting the size, pattern, and arrangement of non-refractive features envisioned in this disclosure such that the desired increase in ganglion cell activity at the individual's retina is balanced against any marginal perception of visual disturbances the individual may experience. In one or more embodiments of this disclosure, the non-refractive features are substantially opaque and positioned within a designated area of ​​the single-vision lens; such that these non-refractive features provide an increase in retinal ganglion cell activity in the light-centric and light-removal-centric retinal pathways disclosed herein. In some methods of this disclosure, non-refractive features may be selected based on the activities the wearer is likely to engage in while wearing the ophthalmic device. For example, a wearer reading or engaging in activities on a computer, table, or telephone may be prescribed a different pattern than a wearer performing a distance vision task, thus maintaining a desired balance between the efficacy of treatment and visual performance. In other methods, non-refractive features may be selected based on potential risk factors for developing or experiencing progressive myopia.

[0065] Several other embodiments, including those discussed in the summary of the invention, are set forth in the specification, drawings, and claims of this disclosure. It is to be understood that it is practically impossible to include every single combination of embodiments contemplated in this disclosure, and any combination or variation of the basic concept of increasing retinal ganglion cell activity by incorporating non-refractive features with ophthalmic lenses is considered to be within the scope of the invention, at least in part. The summary of this disclosure is not intended to limit it to the embodiments disclosed herein. Furthermore, any limitation of one embodiment may be combined with any other limitation of any other embodiment to constitute further embodiments of this disclosure. Attached Figure Description

[0066] Figure 1 The illustrations depict the operation of retinal receptive fields of the light-on-center / light-off-periphery type and the light-off-center / light-on-periphery type according to certain embodiments.

[0067] Figure 2 The illustration shows how the illuminated-central / retracted-peripheral retinal receptive field, according to certain embodiments, operates when subjected to different stimuli or peripheral contour conditions.

[0068] Figure 3 The diagram illustrates a flowchart outlining the operation of a virtual retina platform used to describe some embodiments of this disclosure. The virtual retina platform relies on the following three layers of the retina: the outer retinal layer, the contrast gain control layer, and the ganglion cell layer; as described herein, these retina-related tools help encode visual scenes into a series of action potentials.

[0069] Figure 4 These are basic samples of retinal input images oriented towards retinal receptors, a collection used to illustrate the functionality of a virtual retinal platform for describing the operation of some embodiments of this disclosure.

[0070] Figure 5 The illustration shows the spike sequence (i.e., raster map) and average retinal spike rate for sample neuron locations at the retinal receptor plane for one of the basic retinal configurations disclosed herein. Retinal ganglion cells respond to spatially uniform flickering between black dots on a white background and white dots on a black background.

[0071] Figure 6 The diagram illustrates the spike sequence (i.e., raster plot) and mean retinal spike rate for sample neuronal locations at the retinal receptor plane for another retinal configuration disclosed herein. Retinal ganglion cells respond to spatially uniform flickering between black dots on a white background and white dots on a black background.

[0072] Figure 7 The illustrations show a non-scale front view and cross-sectional view of an exemplary contact lens embodiment having non-refractive features arranged as a plurality of circular apertures as disclosed herein.

[0073] Figure 8 The illustration shows a non-scale front view and cross-sectional view of another exemplary contact lens embodiment having non-refractive features arranged as a plurality of hexagonal apertures as disclosed herein.

[0074] Figure 9 The illustration shows a non-scale front view and cross-sectional view of yet another exemplary contact lens embodiment with stripes as a non-refractive feature, as disclosed herein.

[0075] Figure 10 The illustration shows a non-scale front view and cross-sectional view of yet another exemplary contact lens embodiment with grid lines as a non-refractive feature, as disclosed herein.

[0076] Figure 11 The accompanying figure shows a non-scale front view of three other exemplary contact lens embodiments (i.e., corrugated pattern, curved pattern, and Memphis pattern) as disclosed herein. Only the light-emitting portion of the contact lens is shown in this figure.

[0077] Figure 12 The illustration shows a schematic diagram of theoretical retinal ganglion cell activity recorded by the light-on-center / light-off-periphery retinal circuit and the light-off-center / light-on-periphery retinal circuit when incident light with a certain visible wavelength (e.g., 555 nm) and 0 D convergence is incident on a -3D myopia model eye corrected by a prior art single-view contact lens.

[0078] Figure 13 The illustration shows a schematic diagram of theoretical retinal ganglion cell activity recorded by the light-on-center / light-off-periphery retinal circuit and the light-off-center / light-on-periphery retinal circuit when incident light having a certain visible wavelength (e.g., 555 nm) and 0 D convergence is incident on a -3D myopia model eye corrected by one of the contact lens embodiments disclosed herein.

[0079] Figure 14 The source image file (an image of a mobile phone held at a near viewing distance) represents a wide-field visual scene projected onto the retina of a wide-angle schematic eye using a nonlinear projection routine; wherein the virtual retina is modeled by bundles of neurons arranged in a circular pattern.

[0080] Figure 15 The source image file (an image of a mobile phone held at a moderate viewing distance) represents a wide-field visual scene projected onto the retina of a wide-angle schematic eye using a nonlinear projection routine; wherein the virtual retina is modeled by bundles of neurons arranged in a circular pattern.

[0081] Figure 16 The source image file (Lenna standard image) represents a wide-field visual scene projected onto the retina of a wide-angle schematic eye using a nonlinear projection routine; wherein the virtual retina is modeled by bundles of neurons arranged in a circular pattern.

[0082] Figure 17The illustrations show a non-scale front view and cross-sectional view of an exemplary contact lens embodiment having non-refractive features as a plurality of circular apertures arranged in a hexagonal pattern, as disclosed herein.

[0083] Figure 18 The diagram illustrates the output spike sequences obtained from the light-giving and light-removing cell pathways of a virtual retinal model used for a control lens C1, as described in Example 1 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells (i.e., raster diagrams) are represented as top and bottom subplots. The Y-axis in the diagram represents discrete neuronal bundles, and the x-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0084] Figure 19 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model used for the control contact lens C1, as described in Example 1 of this paper.

[0085] Figure 20 The diagram illustrates the output spike sequences obtained from the light-giving cell pathway and the light-removing cell pathway of the virtual retina model for contact lens implementation D1, as described in Example 1 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents a neuron bundle, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0086] Figure 21 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model for contact lens implementation D1, as described in Example 1 of this document.

[0087] Figure 22 The on-axis modulation transfer functions of the control contact lens C1 and contact lens implementation D1, evaluated at a pupil diameter of 4 mm, as described in Example 1 of this document, are shown.

[0088] Figure 23 The off-axis modulation transfer functions of the control contact lens C1 and contact lens implementation D1, as described in Example 1 of this document, are shown under a field of view of 7.5 degrees and a pupil diameter of 4 mm.

[0089] Figure 24 The illustrations show a non-scale front view and cross-sectional view of an exemplary contact lens embodiment having dot-like non-refractive features arranged in a hexagonal pattern as disclosed herein.

[0090] Figure 25The diagram illustrates the output spike sequences obtained from the light-giving and light-removing cell pathways of a virtual retinal model used for the control lens C2, as described in Example 2 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as the top and bottom subplots, respectively. The Y-axis in the diagram represents discrete neuronal bundles, and the x-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0091] Figure 26 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model used for the control contact lens C2, as described in Example 2 of this document.

[0092] Figure 27 The diagram illustrates the output spike sequences obtained from the light-giving cell pathway and the light-removing cell pathway of the virtual retina model for contact lens implementation D2, as described in Example 2 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents a neuron bundle, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0093] Figure 28 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model for contact lens implementation D2, as described in Example 2 of this document.

[0094] Figure 29 The on-axis modulation transfer functions of the control contact lens C2 and contact lens implementation D2, evaluated at a pupil diameter of 4 mm, as described in Example 2 of this document, are shown.

[0095] Figure 30 The off-axis modulation transfer functions of the control contact lens C2 and contact lens implementation D2, as described in Example 2 of this document, are shown under a field of view of 7.5 degrees and a pupil diameter of 4 mm.

[0096] Figure 31 The illustrations show a non-scale front view and cross-sectional view of an exemplary contact lens embodiment, as disclosed herein, in which stripes are used as a non-refractive feature arranged randomly.

[0097] Figure 32The diagram illustrates the output spike sequences obtained from the light-giving and light-removing cell pathways of a virtual retinal model used for a control lens C3, as described in Example 3 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as the top and bottom subplots, respectively. The Y-axis in the diagram represents discrete neuronal bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0098] Figure 33 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model used for the control contact lens C3, as described in Example 3 of this paper.

[0099] Figure 34 The diagram illustrates the output spike sequences obtained from the light-giving and light-removing cell pathways of a virtual retinal model used for a control lens D3, as described in Example 3 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents discrete neuronal bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0100] Figure 35 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model for contact lens implementation D3, as described in Example 3 of this document.

[0101] Figure 36 The on-axis modulation transfer functions of the control contact lens C3 and contact lens implementation D3, evaluated at a pupil diameter of 6 mm, as described in Example 3 of this document, are shown.

[0102] Figure 37 The off-axis modulation transfer functions of the control contact lens C3 and contact lens implementation D3, as described in Example 3 of this document, are shown under a field of view of 2.5 degrees and a pupil diameter of 6 mm.

[0103] Figure 38 The illustrations show a non-scale front view and cross-sectional view of an exemplary contact lens embodiment with grid lines as a non-refractive feature, as disclosed herein.

[0104] Figure 39The diagram illustrates the output spike sequences obtained from the light-giving and light-removing cell pathways of a virtual retinal model used for a control lens C4, as described in Example 4 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as the top and bottom subplots. The Y-axis in the diagram represents discrete neuronal bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0105] Figure 40 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model used for the control contact lens C4, as described in Example 4 of this paper.

[0106] Figure 41 The diagram illustrates the output spike sequences obtained from the light-giving cell pathway and the light-removing cell pathway of the virtual retina model for contact lens implementation D4, as described in Example 4 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents discrete neuron bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0107] Figure 42 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model used for contact lens implementation D4, as described in Example 4 herein.

[0108] Figure 43 The on-axis modulation transfer functions of the control contact lens C4 and contact lens implementation D4, evaluated at a pupil diameter of 6 mm, as described in Example 4 of this document, are shown.

[0109] Figure 44 The off-axis modulation transfer functions of the control contact lens C4 and contact lens implementation D4, evaluated at a field of view of 7.5 degrees and a pupil diameter of 6 mm, as described in Example 4 of this document, are shown.

[0110] Figure 45 The illustrations are non-scale front views and cross-sectional views of exemplary contact lens embodiments having radially or radially arranged lines or stripes as non-refractive features, as disclosed herein.

[0111] Figure 46The diagram illustrates the output spike sequences obtained from the light-gathering and light-removing cell pathways of a virtual retinal model used for a control lens C5, as described in Example 5 disclosed herein. The spike sequences obtained from the light-gathering cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents discrete neuronal bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0112] Figure 47 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model used for the control contact lens C5, as described in Example 5 of this paper.

[0113] Figure 48 The diagram illustrates the output spike sequences obtained from the light-giving cell pathway and the light-removing cell pathway of a virtual retina model for contact lens implementation D5, as described in Example 5 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents discrete neuron bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0114] Figure 49 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model for contact lens implementation D5, as described in Example 5 of this document.

[0115] Figure 50 The on-axis modulation transfer functions of the control contact lens C5 and contact lens implementation D5, evaluated at a pupil diameter of 5 mm, as described in Example 5 of this document, are shown.

[0116] Figure 51 The off-axis modulation transfer functions of the control contact lens C5 and contact lens implementation D5, as described in Example 5 of this document, are shown at a field of view of 7.5 degrees and a pupil diameter of 5 mm.

[0117] Figure 52 The illustrations show a non-scale front view and cross-sectional view of an exemplary contact lens embodiment having randomly arranged dot-like non-refractive features as disclosed herein.

[0118] Figure 53The diagram illustrates the output spike sequences obtained from the light-giving and light-removing cell pathways of a virtual retinal model used for a control lens C6, as described in Example 6 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as the top and bottom subplots, respectively. The Y-axis in the diagram represents discrete neuronal bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0119] Figure 54 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model used for the control contact lens C6, as described in Example 6 of this paper.

[0120] Figure 55 The diagram illustrates the output spike sequences obtained from the light-giving cell pathway and the light-removing cell pathway of the virtual retina model for contact lens implementation D6, as described in Example 6 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents discrete neuron bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0121] Figure 56 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model for contact lens implementation D6, as described in Example 6 of this document.

[0122] Figure 57 The on-axis modulation transfer functions of the control contact lens C6 and contact lens implementation D6, evaluated at a pupil diameter of 4 mm, as described in Example 6 of this document, are shown.

[0123] Figure 58 Off-axis modulation transfer functions of control contact lens C6 and contact lens implementation D6, evaluated at a field of view of 7.5 degrees and a pupil diameter of 4 mm, as described in Example 6 of this document, are shown.

[0124] Figure 59 The illustrations show a non-scale front view and cross-sectional view of an exemplary contact lens embodiment having helically arranged dot-like non-refractive features as disclosed herein.

[0125] Figure 60The diagram illustrates the output spike sequences obtained from the light-giving and light-removing cell pathways of a virtual retinal model used for a control lens C7, as described in Example 7 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents discrete neuronal bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0126] Figure 61 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model used for the control contact lens C7, as described in Example 7 of this paper.

[0127] Figure 62 The diagram illustrates the output spike sequences obtained from the light-giving cell pathway and the light-removing cell pathway of the virtual retina model for contact lens implementation D7, as described in Example 7 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents discrete neuron bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0128] Figure 63 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model used for contact lens implementation D7, as described in Example 7 of this document.

[0129] Figure 64 The on-axis modulation transfer functions of the control contact lens C7 and contact lens implementation D7, evaluated at a pupil diameter of 6 mm, as described in Example 7 of this document, are shown.

[0130] Figure 65 The off-axis modulation transfer functions of the control contact lens C7 and contact lens implementation D7, evaluated at a field of view of 7.5 degrees and a pupil diameter of 6 mm, as described in Example 7 of this document, are shown.

[0131] Figure 66 The illustration shows a non-scale front view of an exemplary eyeglass lens embodiment disclosed herein with a grid pattern and a prior art eyeglass lens.

[0132] Figure 67The illustration shows a schematic diagram of theoretical retinal ganglion cell activity recorded by the light-on-center / light-off-periphery retinal circuit and the light-off-center / light-on-periphery retinal circuit when incident light with a certain visible wavelength (e.g., 555 nm) and 0 D convergence is incident on a -3D myopia model eye corrected by a prior art single-view contact lens.

[0133] Figure 68 The illustration shows a schematic diagram of theoretical retinal ganglion cell activity recorded by the light-on-center / light-off-periphery retinal circuit and the light-off-center / light-on-periphery retinal circuit when incident light with a certain visible wavelength (e.g., 555 nm) and 0 D convergence is incident on a -3D myopia model eye corrected by one of the contact lenses disclosed herein.

[0134] Figure 69 The illustration shows a non-scale front view of an exemplary spectacle lens embodiment as disclosed herein, which has a dot-shaped non-refractive feature with six radial arms arranged in a spiral pattern.

[0135] Figure 70 The diagram illustrates the output spike sequences obtained from the light-giving and light-removing cell pathways of a virtual retinal model used for a control spectacle lens C8, as described in Example 8 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents discrete neuronal bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0136] Figure 71 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model used for the control spectacle lens C8, as described in Example 8 of this paper.

[0137] Figure 72 The diagram illustrates the output spike sequences obtained from the light-giving cell pathway and the light-removing cell pathway of a virtual retina model for an eyeglass lens implementation D8, as described in Example 8 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents discrete neuron bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0138] Figure 73 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model for the spectacle lens implementation D8, as described in Example 8 of this document.

[0139] Figure 74 The on-axis modulation transfer functions of the control spectacle lens C8 and spectacle lens implementation D8, evaluated at a pupil diameter of 6 mm, as described in Example 8 of this document, are shown.

[0140] Figure 75 The off-axis modulation transfer functions of the control spectacle lens C8 and spectacle lens implementation D8, evaluated at a field of view of 10 degrees and a pupil diameter of 6 mm, as described in Example 8 of this document, are shown.

[0141] Figure 76 The illustration shows a non-scale front view of an exemplary spectacle lens embodiment having non-refractive features arranged in a grid pattern, as described herein.

[0142] Figure 77 The diagram illustrates the output spike sequences obtained from the light-giving and light-removing cell pathways of a virtual retinal model used for a control spectacle lens C9, as described in Example 9 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents discrete neuronal bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0143] Figure 78 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model used for the control spectacle lens C9, as described in Example 9 of this paper.

[0144] Figure 79 The average peak rates obtained from the light-giving and light-removing cell pathways of a virtual retina model for an eyeglass lens implementation D9, as described in Example 9 disclosed herein, are shown. The peak sequences obtained from the light-giving cells and the peak sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot. The Y-axis in the figures represents discrete neuronal bundles, and the X-axis represents time in milliseconds. Dark areas in the figures represent peaks, while white areas represent the absence of peaks.

[0145] Figure 80 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model for the spectacle lens implementation D9, as described in Example 9 of this document.

[0146] Figure 81 The on-axis modulation transfer functions of the control spectacle lens C9 and spectacle lens implementation D9, evaluated at a pupil diameter of 5 mm, as described in Example 9 of this document, are shown.

[0147] Figure 82 Off-axis modulation transfer functions of the control spectacle lens C9 and spectacle lens implementation D9, evaluated at a field of view of 10 degrees and a pupil diameter of 5 mm, as described in Example 9 of this document, are shown.

[0148] Figure 83 The illustration shows a non-scale front view of an exemplary spectacle lens embodiment having randomly arranged linear or striped non-refractive features as disclosed herein.

[0149] Figure 84 The diagram illustrates the output spike sequences obtained from the light-giving and light-removing cell pathways of a virtual retinal model used for a control lens C10, as described in Example 10 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents discrete neuronal bundles, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0150] Figure 85 The average peak rates as a function of time are shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of a virtual retinal model used for the control spectacle lens C10, as described in Example 10 of this paper.

[0151] Figure 86 The diagram illustrates the output spike sequences obtained from the light-giving cell pathway and the light-removing cell pathway of a virtual retina model for an eyeglass lens implementation D10, as described in Example 10 disclosed herein. The spike sequences obtained from the light-giving cells and the spike sequences obtained from the light-removing cells are represented as a top subplot and a bottom subplot, respectively. The Y-axis in the diagram represents a neuron bundle, and the X-axis represents time in milliseconds. Dark areas in the diagram represent spikes, while white areas represent the absence of spikes.

[0152] Figure 87 The average peak rate as a function of time is shown from the light-giving cell (top) pathway and the light-removing cell (bottom) pathway of the virtual retina model for the spectacle lens implementation D10, as described in Example 10 of this document.

[0153] Figure 88 The on-axis modulation transfer functions of the control spectacle lens C10 and spectacle lens implementation D10, evaluated at a pupil diameter of 4 mm as described in Example 10 of this document, are shown.

[0154] Figure 89 The off-axis modulation transfer functions of the control spectacle lens C10 and spectacle lens implementation D10, as described in Example 10 of this document, are shown under a field of view of 10 degrees and a pupil diameter of 4 mm. Detailed Implementation

[0155] Optical solutions available for slowing the rate of myopia progression include some form of optical manipulation of retinal image properties, such as lenses that utilize synchronous defocus, positive spherical aberration, positive focal power, or higher-order aberrations to extend the depth of focus in the center and / or periphery of the optical zone.

[0156] One disadvantage of this optical design is that it compromises visual quality. Given the impact of lens fit on its effectiveness, a significant reduction in visual performance can lead to poorer fit and consequently, worse performance.

[0157] Therefore, what is needed is a design for correcting myopia and slowing its progression that does not cause visual interference associated with manipulating the optical power within the ophthalmic lens. This disclosure proposes an alternative non-refractive method for slowing myopia progression that does not utilize optical defocus as a stop signal. Embodiments of this disclosure propose an alternative method for slowing myopia progression by artificially introducing edge or luminous contrast profiles into the retinal image. Some embodiments further introduce spatiotemporal variations of the luminous contrast profile into the image projected onto the retina through the lens of this disclosure, thereby enhancing overall retinal activity, which in turn can inhibit further eye growth. One or more embodiments of this disclosure rely on the central-peripheral structures of retinal ganglion cells that preferentially respond to spatial and / or temporal variations of the luminous profile incident on the retina.

[0158] In this section, the present disclosure is described in detail with reference to one or more contact lenses or one or more eyeglasses embodiments, some of which are illustrated and supported by the accompanying drawings. Some contact lens embodiments and eyeglasses lens embodiments are provided by way of illustration and should not be construed as limiting the scope of the present disclosure.

[0159] The following description relates to several contact lens and spectacle lens embodiments that may share common 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, which may constitute another embodiment. The functional and structural information disclosed herein should not be construed as limiting in any way and should only be interpreted as a representative basis for teaching those skilled in the art to employ the disclosed embodiments and variations thereof in various ways. Subheadings and related subject headings included in the Detailed Description section are provided for the reader's convenience only and should in no way be used to limit the subject matter described throughout the disclosure or in the claims of this disclosure. Subheadings and related subject headings should not be used to interpret the scope or limitation of the claims.

[0160] Some reported techniques for identifying individuals at risk of developing or progressive myopia include inquiring about one or more of the following factors: genetics, ethnicity, lifestyle, environment, excessive close work, etc. Certain embodiments of this disclosure are directed to individuals identified as being at risk of developing or progressive myopia. To date, numerous optical designs have been proposed to control the rate of eye growth or slow the progression of myopia. Some of these designs are characterized by the use of a certain degree of relative positive focal power associated with the base prescription. Designs based on this optical principle can significantly impair visual quality. Given the impact of lens wear compliance on efficacy, a significant reduction in visual performance can lead to poorer compliance and thus worse efficacy.

[0161] Embodiments of this disclosure relate to the following optical design: utilizing the effect of purposefully configured non-refractive features within the optical zone of another single-vision lens designed to increase retinal ganglion cell activity—which in turn helps to inhibit or slow the rate of myopia progression.

[0162] The human visual system is organized into light-emitting retinal channels or pathways and light-removing retinal channels or pathways. Retinal ganglion cells have circular receptive fields that are organized into light-emitting-central / light-removing-peripheral bipolar cells or light-emitting-peripheral / light-removing-central bipolar cells; Figure 1 and Figure 2 The text provides a concise description of how the receptive field works.

[0163] Complex retinal ganglion cell circuits help to convert spatiotemporal information contained in incident light within a visual input scene into a spike sequence and motion pattern, which is transmitted to the visual cortex via the axons of the fibers that form the optic nerve in the retinal ganglion cells.

[0164] Two groups of retinal ganglion cells—magno cells and parvo cells—help to produce different types of responses to incident light signals captured on the retina. The information carried by the magno cells and parvo cells is parallel and independent of each other.

[0165] Large cell pathways or transient pathways capture the temporal characteristics of incident light signals, such as motion, change, and start within the input scene; while small cell pathways or continuous pathways capture the spatial characteristics of incident light signals, such as patterns and shapes within the input scene.

[0166] The macrocellular pathway has a larger receptive field, shorter latency, and responds instantaneously using rapidly conducting axons. Conversely, the microcellular pathway has a smaller receptive field, longer latency, and responds sustainingly using slower conducting axons. The relative changes captured by the macrocellular pathway and the sustained grayscale image frames captured by the microcellular pathway represent two highly orthogonal representations of a visual scene.

[0167] Given that the regulation of eye growth is local rather than global, macrocellular pathways may be involved in the regulation of eye growth or the mediation of eye growth homeostasis for at least some individuals. In other words, macrocellular retinal ganglion cells, which contain information about local relative changes, provide the ability to encode dynamic or temporal contrasts within a visual scene that can be transcribed into growth initiation or growth cessation signals.

[0168] Increased spatiotemporal contrast in a visual scene has the potential to introduce spikes or short-duration increases in retinal ganglion cell activity; and the more retinal ganglion cell activity there is, the more growth-inhibiting signals are available for the eye. Due to the structure of the retinal receptive field circuitry, retinal ganglion cells cannot be stimulated in two situations: (a) a uniformly illuminated retinal scene without distinct edges (i.e., lack of spatial contrast in the visual scene); or (b) a scene lacking variation for too long (i.e., lack of temporal contrast). The lower the excitation of retinal ganglion cells, the less excitation activity, which in turn indicates less overall retinal activity; and the more inactive states of the retina, the lower the growth-inhibiting signals, leading to further eye growth. The relative difference in the temporal integration of photoreceptive field activity and photoreceptive field deactivation determines further eye growth.

[0169] This disclosure presupposes that an inactive retina triggers eye growth, and an active retina inhibits growth or triggers a stop signal. This disclosure also envisions that standard single-vision contact lenses or spectacle lenses of the prior art, and / or spatially uniform visual images, contribute to the formation of uniform and substantially borderless visual images, thereby keeping the retina in a baseline state (i.e., the baseline pattern or constant excitation pattern of retinal ganglion cells), and thus promoting further eye growth, resulting in deeper myopia.

[0170] Figure 1 The illustrations depict the operation of illuminated-central and illuminated-peripheral retinal receptive fields, as well as illuminated-central and illuminated-peripheral retinal receptive fields, for describing one or more embodiments of the present disclosure.

[0171] Figure 1 The first and third columns highlight four instances of theoretical stimulus representations: (a) no light passes through the retinal receptive field (101 & 111); (b) no light in the central area of ​​the retinal receptive field while the surrounding area is fully illuminated (102 & 112); (c) no light in the peripheral area of ​​the retinal receptive field while the central area is fully illuminated (103 & 113); and (d) both the central and peripheral areas of the retinal receptive field are fully illuminated (104 & 104). The second and fourth columns present examples of... Figure 1 (a) to Figure 1 The various corresponding stimulus conditions disclosed in (d) are the excitation action potentials over time.

[0172] For example, when considering the light-central and light-removal-peripheral retinal receptive fields (i.e. Figure 1 When the light falls on the first two columns, in the absence of light stimulation (101), retinal ganglion cells fire at the basic rate (106). When light falls only on the illuminated-peripheral region and not on the illuminated-central region (102), baseline firing is suppressed during the stimulation phase (107).

[0173] When the spot coincides with the illuminated-central region (103), the excitation rate of retinal ganglion cells is at its maximum (108). When the aperture expands to cover both the illuminated-central region and the de-illuminated-peripheral region (104), the excitation pattern weakens from its maximum and gradually approaches the baseline excitation rate (109).

[0174] When considering the receptive fields of the light-removed center and the light-received periphery (i.e., Figure 1 In the last two columns), without light stimulation (111), retinal ganglion cells are fired at the basic rate (116).

[0175] When light falls only on the illuminated-peripheral region and not on the illuminated-central region (112), the excitation rate of retinal ganglion cells is at its maximum (117). When the light spot coincides with the illuminated-central region (113), baseline excitation is suppressed during the stimulation period (118). When the aperture expands to cover both the illuminated-central and illuminated-peripheral regions (114), the excitation pattern weakens from its maximum and gradually approaches the baseline excitation rate (119). Those skilled in the art will understand that... Figure 1 The illustration represents the theoretically best-case scenario, which is difficult to replicate in real-life settings other than benchtop laboratory experiments.

[0176] Figure 2 It is another graphical representation of the excitation patterns of the retinal receptive fields under different stimuli, including the light-centered and light-deprived peripheral fields. Figure 2 The upper part shows five different light stimulation conditions, which describe some edge detection scenarios that the receptive field may encounter: (i) when the entire receptive field is in the dark part of the edge (201); (ii) when a part of the periphery is in the bright side of the edge while the remaining part of the center and the de-illuminated-periphery region is still in the dark part of the edge (202); (iii) when a part of the de-illuminated-periphery and the illuminated-center region is on the bright side of the edge while most of the illuminated-center and de-illuminated-periphery regions are in the dark spot of the edge (203); (iv) when the entire illuminated-center region is in the bright side of the edge while some part of the de-illuminated-periphery region is on the dark side of the edge (204); and finally (v) when the entire receptive field is in the bright side of the edge (205).

[0177] Figure 2 The lower half of the diagram shows ganglion cell firing action potentials for five different edge detection scenarios (201 to 205) that the receptive field may encounter over time. For example, when the entire receptive field is in the dark part of the edge (201), the firing rate of the ganglion cells is at the baseline rate, which is... Figure 2 The double black solid lines indicate that when a portion of the illuminated-peripheral region is on the bright side of the edge while the illuminated-center remains on the dark side of the edge (202), the firing rate of the ganglion cells is suppressed to below the baseline rate. When portions of both the illuminated-peripheral and illuminated-center regions move toward the bright side of the edge (203), the firing rate returns to the baseline rate. When the entire central region is on the bright side of the edge while some portions of the peripheral region are on the dark side (204), the firing rate reaches its peak.

[0178] Ultimately, when the entire receptive field is in the bright side of the edge (205), the excitation rate decreases to near the baseline rate and is slightly above the baseline rate. The periphery of the receptive field also affects the amount of glutamate released by the photoreceptors. If the surrounding field of view is dark, the photoreceptors in that region will depolarize, resulting in the release of more glutamate.

[0179] When light falls on the illuminated central region while at least some parts of the eclipsed peripheral region experience relative darkness, the horizontal cells of photoreceptors connected to the peripheral visual field depolarize in response to glutamate and release their own inhibitory neurotransmitters. This further inhibits the central photoreceptor, causing it to release even less glutamate. This condition produces the highest response in the excitation action potentials of retinal ganglion cells. The opposite occurs when ambient light is present. The photoreceptors become hyperpolarized in the ambient light, thus releasing less glutamate.

[0180] In response, the horizontal cells connected to photoreceptors in the peripheral visual field will depolarize and release less of their own inhibitory neurotransmitters. This produces a less inhibitory response, allowing the central photoreceptor to remain uninhibited and release even more glutamate. This is the case that will produce the highest response in the delight-central ganglion receptive field.

[0181] Virtual retina model

[0182] It will be understood by those skilled in the art that Figure 2 The illustrations depict theoretical scenarios of various light-providing and light-removing channel retinal visual fields of view, and these may not reflect the typical real-world scenarios experienced by an individual eye. To demonstrate the relevance to various real-life test scenarios, a virtual retinal simulation platform is used to demonstrate the operation of various implementations. The operating principles and technical framework of the virtual retinal platform utilized are described in this paper.

[0183] The virtual retina platform is configured to utilize a set of retinal images, including those in temporal order, as input and to transform this set of retinal images into an output representing a sequence of spikes or action potentials indicating the overall activity of the retina. Essentially, this paper leverages the edge detection capabilities of ganglion cells to provide preferential responses to spatial and / or temporal changes in incoming visual scenes, utilizing the center-periphery structure. Several variables within the framework of the virtual retina platform can be tuned to fine-tune the simulation of wide-area retinal images to mimic real-life scenarios.

[0184] To implement the inventions disclosed herein, some information regarding retinal circuitry and neurophysiology as described in the following scientific articles is required. Therefore, the entire contents of the scientific journal article entitled “Probing thepotency of Artificial Dynamic On- or Off-stimuli to inhibit myopia development,” authored by Wang, Aleman, and Schaeffel and published in the June 2019 issue of *Investigative Ophthalmology and Vision Science*, are cited herein. This article cites in its entirety an article by Wohrer and Kornprobst, titled "Virtual Retina: A biological retina model and simulator, with contrast gain control," published in the Journal of Computational Neuroscience in 2009. It also cites in its entirety an article by Cessac, Kornprobst, Kraria, Nasser, Pamplona, ​​Portelli, and Vieville, published in Frontiers of Neuroinformatics in 2017.

[0185] Ideally, the source input retinal image for the virtual retinal platform should be an approximate representation of an image formed on an individual's human retina when the individual wears one of the embodiments contemplated herein. Since an actual retinal image is unavailable, the operation of the contemplated image can be simulated using an illustrative model eye fitted with the disclosed embodiments, or alternatively, the image can be obtained using a physical model eye fitted with the embodiments disclosed herein.

[0186] When a schematic model eye with a range of refractive errors is fitted with one of the embodiments disclosed herein, this disclosure extensively utilizes advanced ray tracing and schematic modeling to obtain virtual retinal images of various objects. For other embodiments, alternative methods involving the use of physical model eyes or desktop model eyes to demonstrate the operation of the disclosed embodiments may be considered. The operation of various ophthalmic lens embodiments of this disclosure is described using models of the established virtual retinal processing. Figure 3 This is a flowchart illustrating the overall structure of a virtual retina model of the platform used to describe the intrinsic workings of the various embodiments disclosed herein. The model is adapted from the work of Wohrer and Kornprobst, published in a peer-reviewed paper entitled “Virtual Retina: A biological retina model and simulator, with contrast gain control.”

[0187] The proposed three-layer structure of the virtual retina model ( Figure 3 This facilitates a successive spatiotemporal mapping that continuously transmits and transforms input signals present in the virtual scene. The input retinal signal has a brightness curve L(x, y, t); where brightness is defined for each spatially separated point or pixel (x, y) at a time point (t) on the retina. For all simulations used to describe embodiments of this disclosure, the input visual scene is digitized into an intensity between 0 and 255 representing 8-bit gray levels. However, input images with intensities between 0 and 1023, 0 and 4095, or 0 and 65535 representing 10-bit, 12-bit, or 16-bit gray levels can also be used to demonstrate the utility of other embodiments of this disclosure. Subsequent layers of the virtual retinal cells are modeled as a spatial continuum driven by the mathematical equations described herein.

[0188] According to Figure 3 As illustrated in the diagram, the first stage of the virtual retina model involves processing the input signal in the outer reticular layer, which comprises photoreceptors and horizontal cells. In this first stage, a simple spatiotemporal linear filter based on the teachings of Wohrer and Kornprobst, referenced herein, is used to decompose the input sequence L(x, y, t) into the central photoreceptor response C(x, y, t) and the responses S(x, y, t) of the surrounding horizontal cells. Furthermore, the bandpass excitation current I is constrained in the outer reticular layer filter using the responses C(x, y, t) and S(x, y, t). OPL (x, y, t), and then apply the excitation current I. OPL(x, y, t) is fed into the bipolar cell in the second stage of the model. A variable feedback gate with parallel conductance g is used. A (x, y, t) for bipolar layer V BP (x, y, t) is controlled by instantaneous nonlinear contrast gain control to generate an excitation current I. GANG (x, y, t). In the third stage, the discrete equations governing the noise integral and the excitation cell model help to... GANG (x, y, t) is converted into a spike sequence for measuring retinal ganglion cell activity. The spikes can be modeled using one-to-one connections or alternatively using synaptic pooling of the received excitation current.

[0189] To simulate signal transitions occurring in the layers of the retina, multiple linear filters are used at different stages of the model. To simplify computational complexity and minimize computational inefficiencies while maintaining relevance to the real world, several assumptions are made in the model to describe how the embodiments of this disclosure work.

[0190] This disclosure is not limited to the virtual retina model describing the operation of the embodiments, and modifications to the disclosed model and alternative models used for design or verification are considered to be within the scope of the invention. In the first stage of the virtual retina model occurring in the outer reticular layer, the generated current I received by the bipolar cells from the photoreceptors C(x, y, t) and the horizontal cells S(x, y, t) OPL (x, y, t) is obtained as:

[0191] Equation 1:

[0192] Equation 2:

[0193] Equation 3:

[0194] In Equation 1, C(x, y, t) represents the central signal associated with the photoreceptor; and S(x, y, t) represents the peripheral signal associated with the horizontal cell. The phototransduction process is modeled as having a partially transient filter T ωU,τU Modulated exponential time low-pass kernel E τS and gamma exponential cascade E ηC,τC Partial transient linear kernel cascade.

[0195] In Equation 2, the symbol C represents the kernel operation on the center signal, U represents the undershoot, and in Equation 3, S represents the kernel operation on the surrounding signals. The function G in Equation 2... σC This includes spatial blurring of the gaps between photoreceptors.

[0196] The function G in equation 3σS Spatial ambiguity including coupling gaps between horizontal cells. Symbols in Equations 2 and 3. Represents temporal convolution; while the symbol Spatial convolution is represented hereafter. These notations will be used in this disclosure to denote temporal and spatial convolution. The constant λ OPL It is the overall gain of the center-surround filter; while w OPL It is the relative weight of the central signal and the surrounding signals.

[0197] The contrast gain control operation in the second stage of the virtual retina model describes the influence of the local contrast of the visual input scene on the electrical signal transmission characteristics of the retina, an influence that is inherently nonlinear and dynamic. At the bipolar cell level, contrast gain control based on a nonlinear feedback loop can be described as follows:

[0198] Equation 4:

[0199] Equation 5:

[0200] Equation 6:

[0201] In equations 4, 5, and 6, g A The static function QV can be used to represent the bipolar cell membrane. BP Enabled variable leakage. This leakage determines the gain of the current integral at this level, where g A For V BP The evolution of involves splitting. In the model, g A It dynamically depends on the values ​​considered by the bipolar cell, where the time scale is τA and the spatial extent is σA.

[0202] The third stage of the virtual retina model involves generating a spike sequence of retinal ganglion cells based on the activity of bipolar cells. Bipolar signal V BP Rectified and receiving additional spatiotemporal shaping to be used in ganglion cells I GANG An excitation current is generated on (x, y, t), as described in Equations 7 and 8.

[0203] Equation 7:

[0204] Equation 8:

[0205] The models proposed by Wohrer and Kornprobst use empirical formulas to model signal shaping during the transition of currents from bipolar cells to centro-peripheral ganglion cells. These models are suitable for demonstrating the operation of one or more embodiments disclosed herein.

[0206] This model proposes using multiple variables to allow for diversity in the functional reproduction of responses expected by alternative biologically rational models, as described in Equations 7 and 8. The parameter ε takes two input values, -1 and +1, where negative values ​​represent light-reduced ganglion cell activity and positive values ​​are allowed to represent light-received ganglion cell activity.

[0207] The bipolar layer signal is rectified using a static nonlinear function N(V); where the parameter λ G and It has a reduced current magnitude; while This is the linear threshold of ganglion cells. Masmoudi, Antonini, and Kornprobst proposed some alternative models in their paper entitled "Streaming an image through the eye: the retina seen as a dithered scalable image coder," published in the journal Signal Processing: Image Communication, Volume 28 (2013), which is incorporated herein by reference in its entirety. According to I GANG (x, y, t), a series of noise leakage integrals and sets of output spikes generated by excited neurons (nLIF). In the real retina, additional complex conversions of electrical signals occur through the synaptic structures of the inner retina, the site of synaptic interactions between bipolar cells, amacrine cells, and ganglion cells.

[0208] For the purpose of modeling to demonstrate the effectiveness of embodiments of this disclosure, in some examples, the complex synaptic relationships between amacrine cells and bipolar cells are ignored instead of computational efficiency.

[0209] In some other examples, such as those disclosed herein, the complexity of the interactions between horizontal cells and bipolar cells, and the complexity of the interactions between amacrine cells and bipolar cells, are considered. Further extensions of the model are considered to be within the scope of the invention: these further extensions include various other reasonable combinations of interactions between the outer and inner reticular layers to describe the operation of the contemplated ophthalmic lens embodiments of this disclosure.

[0210] The continuous signal I is obtained from the cell's output using the standard nLIF model described by the following equation. GANG Transformation of (X, y, t) into a set of discrete peak sequences:

[0211] Equation 9:

[0212] The standard nLIF model peaks when the following threshold is reached: (V n (t) = 1, and during the refractory period, (V n (t) = 0. Where, (η) ν (t) is a noise source that can be added to the spike generation process to reproduce the variability in real ganglion cells.

[0213] To simulate the spikes of the retinal ganglion cell layer, the following parameters are used to constrain the virtual retina in the model, providing a degree of complexity that offers relative biological plausibility and applicability. Figure 4 The following examples demonstrate the validity of the virtual retina model described in paragraphs

[00179] through

[00200] of this disclosure, which is configured with certain specific retinal parameters described herein.

[0214] In this example, a series of 50 image frames, each with a size of 512×512 pixels, are configured as an image montage to serve as the input source for the virtual retina model. The odd-numbered frames of the video input stream consist of a central circular bright area (401) on a dark background, while the even-numbered frames are configured with a central circular dark area (402) on a white background.

[0215] In this example, each frame is configured to be rendered for 50 milliseconds, equivalent to 2.5 seconds of real-time stimulus rendering for the virtual retinal model. For both odd and even frames of the video input stream, the diameter of the central circular region is configured to be approximately 50 pixels, equivalent to a 0.5° azimuth angle. The bit depth for each pixel in the input stream is digitized to a range of 0 to 255 (i.e., 8 bits). The azimuth angle of the video input stream is configured such that each frame is azimuthated at approximately 5° × 5° on the foveal region of the model retina.

[0216] Two simulation test conditions were used to calculate retinal ganglion cell activity when the input image stream was presented on a virtual retina. The simulation ran with two different cell polarities: a light-on cell mode and a light-off cell mode. Retinal activity was measured by spike activity emanating from the ganglion cell layers of the virtual retina model. The spike activity for each test condition is represented as the average neuronal spike sequence for each bundle and as a histogram of peripheral stimulation showing the average spike rate as a function of time.

[0217] The first test condition includes a neuronal bundle (403) positioned such that the center of the video input stream coincides with the center of the circular neuronal bundle. The second test condition includes seven circular neuronal bundles (404) positioned in a hexagonal pattern, wherein one bundle is located at the center of the video input stream, and the remaining six bundles are arranged circumferentially such that their circumferential diameters are aligned approximately 2.5° × 2.5° in the foveal region of the model retina.

[0218] Furthermore, to illustrate the operation of the virtual retina platform, in this example, the outer mesh layer is configured with a central region facing approximately 1.5° (i.e., σC in Equation 2) and a surrounding region facing approximately 4.75° (i.e., σS in Equation 3). The center timescale and surrounding timescale of the outer mesh layer are set to approximately 1 millisecond, and represent the variables τC in Equation 2 and τS in Equation 3, respectively. As described in Equation 1 of this paper, the variable controlling the integration center-surrounding signal is selected as w. OPL = 1 and λ OPL = 10.

[0219] Given Figure 4 For the simplicity of the input image stimulus characteristics considered in this example, the options for contrasting gain control mechanisms and lateral connectivity without long-processed cells were turned off when computing spike sequences and spike rate analyses. The static nonlinear coefficients for bipolar cell synapses and ganglion cell synapses were modified from Wohrer and Kornprobst, where the bipolar linear threshold was set to 0, while the linear threshold was kept constant at 80, and the bipolar amplification value was kept constant at 100.

[0220] The values ​​for the neuron model were also modified from Wohrer and Kornprobst, where, for Figure 4 , Figure 5 and Figure 6 For the example described, consider a leakage of 0.75, neuronal noise of 20, membrane capacitance of 150, and firing threshold of 2.4. The postsynaptic pooling variable σ is ignored.

[0221] To illustrate the operation of one or more ophthalmic lens embodiments of this disclosure, the static nonlinear coefficients of bipolar cell synapses and ganglion cell synapses can be compared with those used for... Figure 4 The static nonlinear coefficients of bipolar cell synapses and ganglion cell synapses differ in the examples. For example, in some implementations, the bipolar linear threshold can be at least 2, at least 5, at least 10, or at least 15.

[0222] To illustrate the operation of one or more ophthalmic lens embodiments of this disclosure, the linear threshold can be a constant value of at least 30, at least 60, at least 90, or at least 120. To illustrate the operation of one or more ophthalmic lens embodiments of this disclosure, the bipolar magnification value can be at least 50, at least 75, at least 125, or at least 150.

[0223] To illustrate the operation of one or more ophthalmic lens embodiments of this disclosure, the leakage value of the neuron model can be set to at least 0.25, at least 0.5, at least 1, or at least 1.25. To illustrate the operation of one or more ophthalmic lens embodiments of this disclosure, the neuron noise can be set to at least 10, at least 25, or at least 50.

[0224] To illustrate the operation of one or more ophthalmic lens embodiments of this disclosure, the activation threshold of the neuron can be set to at least 1.2, at least 2.4, or at least 3.6.

[0225] In various other exemplary embodiments used to describe the operation of the contact lens and spectacle lens embodiments for use in this disclosure, various configurations with different degrees of complexity can be envisioned, as described in Equations 1 to 9 herein. Specific configuration settings for each of the contact lens embodiments of Examples 1 to 7 are described in the following sections.

[0226] Non-refractive features of the disclosed embodiments

[0227] Because retinal pathways are positioned in the illumination and de-illumination channels in the temporal domain, retinal neurons primarily respond to rapidly increasing (illuminating) or rapidly decreasing (de-illuminating) brightness within a visual scene. In the spatial domain, retinal receptive fields are arranged in a circular pattern within the illumination-center and de-illumination-periphery regions, or vice versa. This arrangement of retinal cells allows for optimized utilization of retinal circuitry to achieve the desired visual processing while maintaining sufficient spatial and / or temporal resolution.

[0228] A clear lack of spatial and / or temporal variation within a visual scene captured at the retinal plane, resulting in poor stimulation of retinal ganglion cells and poor retinal activity, or retinal inactivity, or insufficient retinal activity, is presumed to trigger eye growth. Certain embodiments of this disclosure are intended for individuals at risk of developmental or progressive myopia. One or more embodiments of this disclosure rely on the assumption that a clear lack of distinct edges across the entire retina, temporally varied distinct edges, spatial luminous contrast profiles, or temporally varied spatial luminous contrast profiles may lead to retinal ganglion cell activity similar to the baseline state of the retina; in other words, resulting in substantially retinal inactivity.

[0229] The outputs of all receptive fields are integrated, reflecting the relative intensity of the light input and the light withdrawal input in response to the visual environment. It is assumed that the relative difference in the time integrals of the light-inputting and light-withdrawing receptive field activities determines further eye growth. This disclosure assumes that an inactive retina triggers eye growth, while an active retina inhibits growth or triggers a stop signal.

[0230] This disclosure further envisions that the standard single-vision ophthalmic lens and / or spatially uniform visual image of the prior art helps to produce a uniform and spatially borderless visual image, thereby keeping the retina in a baseline state (i.e., the baseline or constant excitation pattern of retinal ganglion cells) and thus promoting further eye growth, resulting in greater myopia.

[0231] One or more of the following advantages are found in one or more of the disclosed optical devices and / or the methods for designing ophthalmic lenses disclosed herein. The ophthalmic lens or method provides a stopping signal based on increased retinal activity by employing multiple non-refractive features and artificially introducing an edge or enhanced luminous spatial contrast profile or enhanced temporal contrast profile into a retinal image generated by means of a configuration of the conceived design features on the ophthalmic lens, thereby slowing the rate of eye growth in the wearer's eye, or halting the increase in the rate of eye growth or refractive error in the wearer's eye.

[0232] The upward eye movement of the contact lens can further enhance the intensity of the treatment effect by providing spatially and temporally varying cessation signals, thereby improving the effectiveness of managing progressive myopia.

[0233] Some other implementations involve contact lens devices or methods that are not solely based on optical manipulation including defocus, astigmatism, or positive spherical aberration, all of which may suffer from potential deterioration of visual performance for the wearer. The following exemplary implementations relate to methods of modifying incident light using ophthalmic lenses that can selectively influence eye growth and myopia progression using illuminated and deilluminated visual pathways.

[0234] The following exemplary embodiments relate to a method of modifying incident light using an ophthalmic lens that provides increased retinal ganglion activity by artificially introducing inhomogeneities into the visual image and creating or increasing a luminous contrast profile (i.e., an artificial edge) at the retinal plane of the corrected eye to stimulate the light-giving pathway. This can be achieved by using generally opaque boundaries of multiple apertures, zones, segments, or regions within other single-vision optical zones of the ophthalmic lens.

[0235] In short, the proposed use of multiple apertures, non-refractive regions, or non-refractive areas within the optical zone of other single-vision contact lenses or spectacle lenses can increase the activity of retinal ganglion cells by stimulating the light-giving and / or light-withdrawing pathways generated by artificially introduced spatial edge contours as light passes through the contact lens or spectacle lens.

[0236] Furthermore, this use of the excitation area, non-refractive area, or multiple apertures within a single-vision contact lens or spectacle lens can provide variations in temporal contrast supplemented by eye movements and / or blinking of the eyelids using the contact lens and ophthalmic lens embodiments disclosed herein.

[0237] Indicative eye & simulated retina image

[0238] An advanced, illustrative model eye can be used to calculate wide-area simulated retinal images and wide-area optical performance for one or more exemplary embodiments disclosed herein.

[0239] Table 1 below provides a general prescription for obtaining an illustrative model eye that serves as input to a virtual retinal platform used to simulate the operation of embodiments of the present disclosure. The parameters described in Table 1 are not essential to demonstrating the described effects obtained through embodiments of the present disclosure. This should be considered as one of several methods for obtaining an illustrative model eye to facilitate the simulation of retinal processing performed by the virtual retinal platform described herein. For example, in other exemplary embodiments, other model eyes from the literature may be used instead of the model eye described in Table 1. The general parameters of the illustrative model eye used are based on the prescriptions listed in Table 1. In this example, the general prescription in Table 1 provides an illustrative model eye configured to be in its unadapted state, with a distance refractive error of 1 D myopia without any astigmatism (Rx: -1 D), wherein the distance prescription for the model eye is defined at a pupil diameter of 6 mm and a dominant wavelength of 589 nm.

[0240] Table 1: Prescriptions for a schematic model eye with a distance refractive prescription of -1 D.

[0241] In the various other exemplary embodiments disclosed herein, various modifications can be considered to evaluate the performance of other ophthalmic lenses described herein. Furthermore, various parameters of the illustrative model eye—such as the anterior cornea, posterior cornea, corneal thickness, anterior lens, posterior lens, lens thickness, refractive index of the ocular media, retinal curvature, or combinations thereof—can be varied to demonstrate the working principle of this disclosure in various degrees of myopia, with or without astigmatism, and for modeling various myopic eyes in relaxed and adapted states.

[0242] To obtain a wide-field simulated retinal image using a schematic model eye equipped with various embodiments of this disclosure, the source image file is convolved with an array of point spread functions spanning the desired field of view, as disclosed herein, considering the nonlinear projection of the visual scene into the wide-angle schematic eye. Figure 14 , Figure 15 and Figure 16 The document shows three source image files used in one or more implementations. Figure 14 The first source image shown on the left side is a source image file of a mobile phone screen display against a white background, wherein the mobile phone screen display is configured with some clear characters, and the opposing angle of the source scene is configured to capture a 15-degree field of view at a viewing distance of 50 cm.

[0243] Figure 14 A source image file representing a wide-field visual scene (1401) projected onto the retina of a wide-angle schematic eye using a nonlinear projection routine; wherein the virtual retina is modeled by bundles of neurons arranged in a circular pattern (1402). In various embodiments, both the wide-field visual scene (1401) of the mobile phone against a white background and the frame (1402) representing the virtual retina are oriented towards the retinal field of view at approximately 5°, 15°, or 20°. Figure 15 The second source image shown in the left part of the diagram is another mobile phone screen display on a white background screen, where the mobile phone screen display is configured with some clear characters, and the opposing angle of the source scene is configured to capture a 15° field of view at a viewing distance of 1 meter.

[0244] Figure 15 A source image file representing a wide-field visual scene (1501) projected onto the retina of a wide-angle schematic eye using a nonlinear projection routine; wherein the virtual retina is modeled using bundles of neurons arranged in a circular pattern (1502). In various embodiments, both the wide-field visual scene (1501) of the mobile phone against a white background and the frame (1502) representing the virtual retina are oriented towards the retinal field at approximately 5°, 15°, or 20°. Figure 16 The third source image file shown on the left side is the source image file of an 8-bit grayscale Lennara image; the Lennara image can be configured into two variants to face the field of view at a viewing distance of 6 meters at 5 degrees, 15 degrees, or 20 degrees.

[0245] Figure 16 A source image file representing a wide-field visual scene (1601) projected onto the retina of a wide-angle schematic eye using a nonlinear projection routine; wherein the virtual retina is modeled using bundles of neurons arranged in a circular pattern (1602). In various embodiments, both the wide-field visual scene (1601) of a standard Lenna test image represented in 8-bit grayscale and the frame (1602) representing the virtual retina are oriented towards the retinal field at approximately 5°, 15°, or 20°.

[0246] For each pixel in the modified image file, an array of point spread functions is interpolated. At each pixel, the effective point spread function is convolved with the modified source image file.

[0247] In order to calculate the point spread function at the desired field, Huygens' principle has been modified in this disclosure because the modeling effect of relatively small non-refractive features may be affected by the Fourier estimate, which is usually used to improve computational efficiency.

[0248] The calculation of the array of point spread functions spanning the desired field of view includes the effects of diffraction and aberration. The resulting simulated retinal image is scaled and stretched to account for the detected level of distortion. The brightness of the simulated retinal image is determined by normalizing the intermediate output image to have the same peak brightness as the input source image considered by the convolution operation disclosed herein.

[0249] In various embodiments of this disclosure, the settings of various parameters required for simulating virtual retinal images are varied to capture a variety of real-life scenarios that an individual may experience.

[0250] In some implementations, since the accuracy of retinal image simulation is limited by the resolution of the input source image, care should be taken to maintain an input image resolution of at least 512×512 pixels to avoid significant pixel discretization of the output image, which is usually exhibited by aliasing effects. Furthermore, if necessary, oversampling of the input source is considered to minimize this effect at the cost of relatively long computation time.

[0251] Contact lens implementation

[0252] Figure 7A non-scale front view and cross-sectional view of an exemplary contact lens embodiment are shown. The front view of the exemplary contact lens embodiment further illustrates the optical region (701), the lens diameter (702), and several non-refractive features (703) of the contemplated design.

[0253] In this exemplary example, the lens diameter is approximately 14 mm, the optical zone is designed to have approximately single-view refractive power, and the diameter of the optical zone is approximately 8 mm. Non-refractive features are arranged within the optical zone in the form of multiple circular apertures, each non-refractive feature having a diameter of approximately 1 mm. The boundaries of these non-refractive features (703) arranged in the form of multiple circular apertures can be configured to be between completely opaque and substantially opaque. For example, the transmission characteristics of the non-refractive features—in this example, the boundaries of multiple circular apertures—can be configured such that greater than 95% of the light incident on the non-refractive features or boundaries is absorbed or not transmitted.

[0254] Figure 7 The boundaries of the multiple circular apertures envisioned herein, i.e., the width of the non-refractive feature, are approximately 50 μm (704). This is magnified relative to the size of the contact lens described herein to demonstrate and enhance the legibility of the feature. The remainder of the optical zone, without the envisioned non-refractive feature—which includes the transparent areas within the multiple apertures—includes a single-vision design that matches the wearer's basic prescription.

[0255] Figure 8 A non-scale front view and cross-sectional view of another exemplary contact lens embodiment are shown. The front view of the exemplary contact lens embodiment further illustrates the optical region (801), the lens diameter (802), and a plurality of interconnected hexagonal non-refractive features (803) of the contemplated design. In this exemplary example, the lens diameter is approximately 14.2 mm, the diameter of the optical region, designed to have approximately single-view refractive power, is approximately 9 mm, and the maximum diameter of each of the non-refractive features arranged within the optical region in the form of the boundaries of a plurality of hexagonal apertures is approximately 1 mm.

[0256] The boundaries (803) of these non-refractive features, arranged in the form of multiple hexagonal apertures, can be configured to be between completely opaque and translucent. For example, the transmission properties can be configured such that more than 90% of the light incident on the non-refractive features or boundaries is absorbed or not transmitted.

[0257] Figure 8The boundaries of the envisioned multiple hexagonal apertures, i.e., the width of the non-refractive feature, are approximately 25 μm (804). This is magnified relative to the size of the contact lens described herein to demonstrate and enhance the legibility of the feature. The remainder of the optical zone, without the envisioned non-refractive feature—which includes the transparent areas within the multiple apertures—includes a single-vision design that matches the wearer's basic prescription.

[0258] In another embodiment of the contact lens, the plurality of non-refractive features may be arranged as the boundaries of a plurality of circular, semi-circular, elliptical, hexagonal, or any other polygonal apertures, wherein the plurality includes at least 2, 3, 5, 7, 9, 12, or 15 non-refractive features.

[0259] In some other contact lens embodiments, the number of non-refractive design features arranged in the form of multiple polygonal aperture boundaries can be between 4 and 7, or between 3 and 9, or between 2 and 12, or between 3 and 15. In some embodiments, the non-refractive design features arranged in the form of multiple aperture boundaries can be separated, while in other embodiments, these non-refractive design features can be adjacent or connected.

[0260] In yet another embodiment of the contact lens, the non-refractive features configured as the boundaries of multiple apertures, regions, segments, or sections can be arranged within 1 mm, 2 mm, 3 mm, 4 mm, 5 mm, or 6 mm of the center of the optical area of ​​the contact lens. In yet another embodiment of the contact lens, as disclosed herein, the non-refractive features configured as the boundaries of multiple apertures, regions, segments, or sections can be arranged between 1 mm and 3 mm of the center of the optical area of ​​the contact lens, or between 2 mm and 4 mm of the center, or between 3 mm and 5 mm of the center, or between 2 mm and 6 mm of the center.

[0261] In some contact lens embodiments, the width of the completely opaque, substantially opaque, or translucent boundary of the contemplated non-refractive design feature within the optical region of the contact lens can be at least 5 μm, 10 μm, 20 μm, 30 μm, 40 μm, or 50 μm. In some contact lens embodiments, the width of the opaque boundary of the contemplated non-refractive design feature within the optical region of the contact lens can be between 5 μm and 15 μm, between 15 μm and 25 μm, or between 10 μm and 50 μm.

[0262] In some other embodiments, the boundary of the contemplated non-refractive design feature within the optical region of the contact lens may be opaque, while in still other embodiments, the boundary of the contemplated design feature may be translucent. In some embodiments, the width of the boundary or design feature may not be constant across the plurality of apertures. In one embodiment of this disclosure, the shapes of the plurality of apertures may also be different.

[0263] Figure 9 A non-scale front view and cross-sectional view of another exemplary contact lens embodiment are shown. The front view of the exemplary contact lens embodiment further illustrates the optical region (901), the lens diameter (902), and several non-refractive features (903) of the contemplated design.

[0264] In this exemplary example, the lens has a diameter of approximately 14.5 mm, the optical zone designed to have approximately 14.5 mm diameter has approximately 8 mm diameter, and the non-refractive features configured as lines or stripes have a length of approximately 2 mm. These non-refractive features (903) may be substantially opaque; wherein 95% of the light incident on the non-refractive features is not transmitted or absorbed.

[0265] Figure 9 The width (904) of the envisioned non-refractive feature is approximately between 25 μm and 50 μm, and this width is only magnified in the figures relative to the size of the contact lens described herein to illustrate the feature. In a preferred embodiment, the maximum width of the non-refractive feature does not exceed 100 μm, 150 μm, or 200 μm to avoid any undesirable impact on resolution characteristics. The remainder of the optical zone without the envisioned non-refractive feature—which includes transparent areas within multiple apertures—includes a single-vision design that matches the wearer's basic prescription.

[0266] Figure 10 A non-scale front view and cross-sectional view of another exemplary contact lens embodiment are shown. The front view of the exemplary contact lens embodiment further illustrates the optical region (1001), the lens (1002), and the non-refractive feature (1003).

[0267] In this example, the lens diameter is approximately 14 mm, and the diameter of the optical zone designed to have approximately single-view refractive capability is approximately 8 mm. A contemplated design feature of this embodiment is a grid pattern positioned at the center of the contact lens, spanning approximately 3 mm in both height and width. The boundaries (1003) of these grid lines can be configured to be completely opaque or substantially opaque. Figure 10The width (1004) of the non-refractive feature envisioned in the figure is approximately between 50 μm and 100 μm. This width of the non-refractive feature is only magnified in the figure relative to the size of the contact lens described herein to show the feature.

[0268] Figure 10 The implementation can also be configured in other variations, for example, the width of the envisioned non-refractive design feature within the optical region can be at least 5 μm, 10 μm, 20 μm, 30 μm, 40 μm or 50 μm. Figure 10 The implementation can also be configured in other variations; for example, the width of the envisioned non-refractive design feature within the optical region can be between 5 μm and 15 μm, between 15 μm and 25 μm, or between 10 μm and 50 μm. Figure 10 In a preferred variant of the implementation, the maximum width of the non-refractive feature, i.e. the width of the lines forming the grid pattern, does not exceed 150 μm, 200 μm, or 250 μm, in order to avoid any unnecessary impact on the resolution characteristics of the eye.

[0269] In other embodiments, the envisioned non-refractive feature may be positioned within the periphery of the optical zone. In yet another contact lens embodiment, the number of lines or stripes forming the grid pattern may be at least 5, 9, 15, or 25. In some other contact lens embodiments, the design feature, i.e., the number of lines or stripes forming the grid pattern, may be between 5 and 9, or between 9 and 15, or between 9 and 15, or between 5 and 25. In another embodiment, a single, generally uninterrupted long curve or zigzag line with a length of at least 3 mm, 6 mm, 9 mm, or 12 mm is conceivable.

[0270] In another contact lens embodiment, one or more stripes can be arranged symmetrically or randomly, and these stripes can be concentric or off-center from the optical axis. The stripes can also be composed of straight lines or curves, and can be in contact with or intersect each other, or be completely separate, or a combination of the foregoing. The stripes can vary in width and length. Lenses worn in the left and right eyes can have different patterns.

[0271] In yet another embodiment of the contact lens, the envisioned design features (i.e., multiple stripe patterns or wavy patterns) may be separated from each other within the optical area of ​​the contact lens. In yet another embodiment, the envisioned multiple non-refractive features may be configured to be adjacent to or interleaved with each other.

[0272] Because the combined movement of the upper and lower eyelids promotes natural blinking, the contact lens can move freely relative to the wearer's eyeball. This can result in temporally varying stimuli, which further enhances the inhomogeneity artificially introduced into the visual image, thereby reducing the rate of myopia progression in myopia wearers.

[0273] Figure 11 Three additional exemplary contact lens embodiments are shown in non-scale front views. The front views of the exemplary contact lens embodiments illustrate only magnified views of the optical zone (1101) and three contemplated non-refractive design features (1103a, 1103b, and 1103c). In this example, the non-refractive design feature (1103a) is a representative example of the contemplated corrugated pattern configured away from the center of the contact lens embodiment.

[0274] Non-refractive design feature (1103b) illustrates another representation of a hypothetical spiral pattern passing through the optical zone. Non-refractive design feature (1103c) illustrates a Memphis pattern with respect to the optical center alignment of the contact lens. The optical zone is designed to have approximately single-view refractive power, and the diameter of the optical zone is approximately 8 mm. The width of the design feature ranges from 5 μm to 100 μm, and the generally opaque feature in the figure is highlighted relative to the size of the contact lens described herein to illustrate the feature.

[0275] In another contact lens embodiment, the design features (i.e., multiple non-refractive stripes or wavy patterns) may be located within 1 mm, 2 mm, 3 mm, 4 mm, 5 mm, or 6 mm of the center of the optical region of the contact lens. In yet another contact lens embodiment, the design features (i.e., multiple non-refractive stripes or wavy patterns) may be located between 1 mm and 3 mm, or between 2 mm and 4 mm, or between 3 mm and 5 mm, or between 2 mm and 6 mm of the center of the optical region of the contact lens. In yet another contact lens embodiment, the contemplated design features (i.e., multiple stripe patterns or wavy patterns) may be separated from each other within the optical region of the contact lens. In yet another embodiment, the contemplated multiple non-refractive features may be configured to be adjacent to or staggered. In some contact lens embodiments, the width of the contemplated non-refractive design features (i.e., multiple stripe patterns or wavy patterns) within the optical region of the contact lens may be at least 5 μm, 10 μm, 20 μm, 30 μm, 40 μm, or 50 μm.

[0276] In some contact lens embodiments, the width of the contemplated non-refractive design feature within the optical region of the contact lens can be between 5 μm and 15 μm, 15 μm and 25 μm, or 10 μm and 50 μm. In some other embodiments, the boundary of the contemplated non-refractive design feature within the optical region of the contact lens can be opaque, while in still other embodiments, the boundary of the contemplated design feature can be translucent. In some embodiments, the width of the design feature may not be constant across multiple non-refractive features.

[0277] Figure 12 A schematic diagram is shown depicting incident light from a wide field of view (1201) into a 2D myopic model eye (1200) with a focal length of 0D and a visible wavelength of, for example, 555 nm, which is corrected by a standard single-vision lens (1202) of the prior art.

[0278] When a standard single-lens reflex (1202) of the prior art moves on the anterior surface of the eye due to natural blinking, habitual eye movements, or a combination of natural blinking and habitual eye movements, retinal ganglion cell activity is recorded by the light-center / light-withdrawal-periphery circuit and the light-withdrawal-center / light-center-periphery circuit (1203), thus demonstrating or illustrating minimal retinal activity or retinal activity at the baseline rate. The relative difference in the time integrals of light-receptor field activity and light-withdrawal receptive field activity determines further eye growth.

[0279] This disclosure presupposes that an inactive retina triggers eye growth, while an active retina inhibits growth or triggers a stop signal. This disclosure further envisions that standard single-vision contact lenses or spectacle lenses of the prior art and / or spatially uniform visual images contribute to the production of uniform and spatially largely borderless visual images, thereby keeping the retina in a baseline state (i.e., the baseline or constant firing pattern of retinal ganglion cells), and thus promoting further eye growth, resulting in greater myopia.

[0280] Figure 13A schematic diagram is shown depicting an incident beam of light with a focal length of 0 D from a wide field of view (1301) into a 2D myopia model eye (1300) having a visible wavelength, for example 555 nm, corrected using an exemplary implementation (1302) of the exemplary embodiments disclosed herein. When the exemplary implementation (1302) moves on the anterior surface of the eye due to natural blinking, habitual eye movement, or a combination of natural blinking and habitual eye movement, retinal ganglion cell activity is recorded by an illumination-center / withdrawal-periphery circuit and an illumination-center / withdrawal-periphery circuit (1303), thereby demonstrating or illustrating increased activity at the retina compared to a baseline state.

[0281] For illustrative purposes, in Figure 12 and Figure 13 A simple model eye has been chosen in this embodiment; however, in other embodiments, illustrative ray-traced model eyes such as those of Liou-Brennan and Escu Dero-Navarro can be used instead. The examples provided herein have used a 2D myopic model eye to disclose the invention; however, this disclosure can be extended to other degrees of myopia, namely -1D, -3D, -5D, or -6D. Furthermore, it should be understood that this can be extended to eyes with varying degrees of combined myopia and astigmatism. In the embodiments, the specific wavelength of 555 nm is mentioned; however, it should be understood that this can be extended to other visible wavelengths between 420 nm and 760 nm.

[0282] Modeling of various exemplary contact lens implementations (D1 to D7) demonstrates that the envisioned non-refractive features used in conjunction with a single-view optical profile provide an increase in retinal ganglion cell activity, which is measured by an increase in the average retinal peak rate obtained using the virtual retina platform disclosed herein.

[0283] In other implementations, various alternative measurements of retinal ganglion cell activity may be considered, such as examining spike sequence analysis for selected neuronal bundles.

[0284] To illustrate the operation of the contact lens embodiments according to the invention, improved optical modeling experiments were conducted using two different types of contact lenses for each test condition (i.e., Examples 1 to 7) as described herein. The first type includes monocular control contact lenses (C1 to C7), which are matched to the basic prescription of the illustrative model eye to provide correction of refractive errors, thereby simulating standard treatment. The second type includes various exemplary contact lens embodiments (D1 to D7) that are essentially identical to the monocular, standard treatment control contact lenses (C1 to C7), but which are further configured with additional non-refractive features designed according to the invention.

[0285] To illustrate the operation of the invention, controls (C1 to C7) and exemplary contact lenses (D1 to D7) were fitted, tested / evaluated one at a time on the modified schematic eye models described in Examples 1 to 7. For the purpose of demonstrating the operation of these Examples 1 to 7, only the optical area (8 mm) of the contact lens was modeled. In other examples, the entire contact lens, including the peripheral area and edges, may be modeled as needed.

[0286] The surface transmittance characteristics of the front surface of the contact lens are modified to design the features of Examples 1 through 7. Transmittance is calculated as a fraction of 100%, where 100% means that all light is transmitted as if there were no absorption, reflection, or vignetting loss. In some embodiments of this disclosure, surface transmittance is defined as a relatively arbitrary percentage of the intensity of rays transmitted through the surface. In some other embodiments of this disclosure, the relatively arbitrary percentage of intensity can be configured to be wavelength-dependent. In some other embodiments of this disclosure, the arbitrary percentage of intensity can be configured to be polarity-sensitive.

[0287] To assess simulated retinal ganglion cell activity, a contact lens was slid across the anterior corneal surface at various off-center positions to simulate supraocular lens movement during vertical blinking and / or relative lens movement that might occur during horizontal saccadic eye movements. The movement of the contact lens relative to the center of the anterior corneal surface was within + / -1 mm in both the horizontal and vertical directions. Both off-center and tilt functions were used in the modeling device to simulate supraocular lens movement.

[0288] Wide-area retinal image simulations are performed at each off-center lens location. Forty-eight (48) such simulated retinal images constitute the input stream for the virtual retinal platform to generate retinal ganglion cell activity. In this example, each of the 48 image frames is configured for 50 milliseconds, equivalent to a real-time stimulus display of the virtual retinal model for 2.4 seconds. Each frame of the input stream is configured to exceed 512 × 512 pixels, wherein each frame is configured to cover the full diameter of the circular neuronal region, thereby surrounding an area of ​​approximately 5° × 5° (fovea) or 15° × 15° (macula) of the retina of the virtual retinal platform. The bit depth for each pixel in the input stream is digitized to a range from 0 to 255 (i.e., 8 bits). The specific retinal setup and configuration described in Equations 1 through 9 for demonstrating the operation of the contact lens implementation of this disclosure are discussed in the following sections.

[0289] In all Examples 1 through 7, the outer mesh layer is configured with a central region facing approximately 1.5° (i.e., σC in Equation 2) and a surrounding region facing approximately 4.75° (i.e., σS in Equation 3). The center and surrounding time scales of the outer mesh layer are set to approximately 1 millisecond, and are represented by the variables τC and τS in Equations 2 and 3, respectively. As described in Equation 1 of this paper, the variable controlling the integration center-surrounding signal is selected as w. OPL =1 and λ OPL =10. The static nonlinear coefficients of bipolar cell synapses and ganglion cell synapses are fixed in all Examples 1 through 7. The bipolar linear threshold is set to 0, the linear threshold is kept constant at 80, and the bipolar amplification value is kept constant at 100.

[0290] The values ​​used for the neuron model are maintained throughout Examples 1 through 7, where, for the simulations in Examples 1 through 7, the leakage is 0.75, neuronal noise is 20, membrane capacitance is 150, and the firing threshold is 2.4. The postsynaptic pooling variable σ is ignored. The options for the contrast gain control mechanism, the utility of the supplementary high-pass filter in the outer reticular layer, and the utility of lateral connectivity without long-processed cells remain variable in Examples 1 through 7. Further details of the specific settings used are disclosed herein.

[0291] Example 1 – Comparative (C1) Design and Exemplary Implementation (D1) Design

[0292] In this example, the following parameters of the schematic model eye in Table 1 are modified to configure a 1D myopic eye in its 2D adaptation state (i.e., the basic prescription Rx is -1D): (1) the radius of curvature of the anterior lens (R = 8.22 mm); and (2) the conic constant of the anterior lens (Q = -2.314). The model is configured to focus on a near object approximately 50 cm away from the eye. The modified schematic model eye for myopia is corrected one at a time using a control (C1) contact lens and an exemplary embodiment (D1) contact lens. The control contact lens C1 is modeled using an anterior surface radius (R = 7.936 mm, Q = -0.221), a central thickness (0.135 mm), a posterior surface radius (R = 7.75 mm, Q = -0.25), and a refractive index of 1.42. The control contact lens C1 has no / lacks any non-refractive features contemplated in this disclosure.

[0293] The exemplary embodiment (D1) contact lens is a single-view contact lens having the same optical design as the control (C1), and the exemplary embodiment (D1) contact lens is further configured with, as Figure 17 The disclosed additional non-refractive features.

[0294] Figure 17 A non-scale front view and cross-sectional view of an exemplary contact lens embodiment D1 are shown. The front view of the exemplary contact lens embodiment further illustrates the optical region (1701), the lens diameter (1702), and a plurality of non-refractive features (1703), which include interconnected circular non-refractive features of the contemplated design (D1). The total number of circular apertures is 7. The total diameter of the non-refractive features including the plurality of apertures is approximately 3.75 mm. The diameter of each aperture is approximately 1.25 mm. The width of the boundary of each aperture is approximately 100 μm (1704).

[0295] For identification and readability, the non-refractive features are magnified relative to the other features of the contact lens. The remainder of the non-refractive features of the optical zone (1701) without exemplary embodiment D1 is configured with basic monocular prescription parameters that match the basic prescription of the eye.

[0296] In this exemplary example D1, the lens diameter is approximately 14.2 mm, the diameter of the optical zone designed to have approximately single-vision refractive capability is approximately 8 mm, and the diameter of each of the non-refractive features arranged in the optical zone in the form of multiple circular apertures is approximately 1 mm. Following the steps disclosed in paragraphs

[00271] to

[00273] , simulated retinal images are calculated and analyzed one at a time by means of the control C1 contact lens design and the embodiment D1 contact lens design mounted on the illustrative model eye of Example 1.

[0297] In this Example 1, the additional variables of the virtual retina platform are conceived to have the following settings; the options for the contrast gain control mechanism described in Equations 1, 5, and 6 are used in conjunction with the following input parameter values: (i) the amplification λ of the outer mesh layer per normalized luminance unit. OPL The value is 150 Hz; (ii) Bipolar inert leakage (iii) Feedback amplification λ A The Hz value is 100 Hz; (iv) the spatial scale σA is 2.5°; and (v) the temporal scale τA is 0.01 ms. The neuron bundles (1402) are arranged in a circular pattern spanning a 15° × 15° field of view.

[0298] The sparse lateral connectivity mode of the virtual retina was used with 10 presynaptic neurons having 10% positive weights and a weight variance of 0.01. Furthermore, the supplementary high-pass filter option for the outer reticular layer described in Equations 2 and 3 was not used. The postsynaptic pooling option was turned off.

[0299] Post-processing of the simulated retinal image calculated from the control (C1) contact lens design of Example 1 was performed using the virtual retina platform as described herein, generating a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 18 ) and the histogram of surrounding stimuli, which is a function of time, highlighting the average peak rate ( Figure 19 ). Figure 18 and Figure 19 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0300] Post-processing of the simulated retinal image calculated for the contact lens design of Example 1 (D1) using the virtual retina platform as described herein generated a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 20 ) and the histogram of surrounding stimuli, which is a function of time, highlighting the average peak rate ( Figure 21 ). Figure 20 and Figure 21 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0301] For cells with two types of polarity—light-giving polarity and light-removing polarity—the following is described in the case of a control (C1) contact lens: Figure 18 The neuronal activity of the spike sequence is either constant or monotonic as a function of time.

[0302] On the other hand, for cells with two types of polarity—light-giving polarity and light-removing polarity—the description in the case of the contact lens in embodiment (D1) is as follows: Figure 20 The neuronal activity of the spike sequence as a function of time is either time-varying or non-monotonic.

[0303] In Example 1, the depiction is as follows in the case of the contact lens (C1): Figure 19 The average peak rate of neuronal activity follows a monotonic profile after the initial 100 ms of signal stabilization. This observed pattern is similar for cells with two types of polarity—light-giving polarity and light-removing polarity. In Example 1, after the initial 100 ms stabilization period, the average peak rate for light-giving cells in the case of the control (C1) contact lens is approximately one-quarter (1 / 4) the size of the average peak rate obtained in the case of light-removing cells, as disclosed herein. Figure 19 On the other hand, the depiction in the case of the contact lens in embodiment (D1) is as follows: Figure 21 The average peak rate of neuronal activity as a function of time is either time-varying or non-monotonic.

[0304] In Example 1, the average peak rate obtained by the contact lens of embodiment (D1) for light-bearing cells is at least 3 to 4 times that obtained by the control (C1) contact lens for light-bearing cells. In this example, as Figure 21 As shown, for both light-giving and light-removing cells, the average peak rate as a function of time obtained by the contact lens in embodiment (D1) follows a quasi-sine pattern.

[0305] The instability and nonlinearity in the peak response obtained by implementing the lens are attributed to artificial edges or luminous contrast profiles in the retinal image, or the temporal variation of artificial edges.

[0306] In Example 1, under photopic vision conditions and with a pupil analysis diameter of 4 mm, on-axis and off-axis evaluations of optical performance are modeled using a photometric function describing the average spectral sensitivity of human visual perception of brightness in a multicolor mode spanning from 470 nm to 650 nm.

[0307] As in this article Figure 22 and Figure 23The wide-area optical performance, measured using a modulation transfer function as a function of spatial frequency at a pupil diameter of 4 mm, is remarkably similar between the control (C1) contact lens and the exemplary embodiment (D1) contact lens, i.e., the area below the curve represented by the solid black line and the area below the curve represented by the dashed black line have a variation of less than 5%. In Example 1, for off-axis performance, a field of view of 15° is considered for performance evaluation, i.e., ±7.5° from the center.

[0308] Example 2 – Comparative (C2) Design and Exemplary Implementation (D2) Design

[0309] In this example, the following parameters of the illustrative model eye in Table 1 are changed to represent a 2D myopic eye with 1 DC astigmatism in its 2D adaptation state (i.e., the basic prescription Rx is -2D / -1DC): (i) the anterior corneal curvature radius along the X-axis (R x = 7.829mm); (ii) Anterior corneal conic constant along the X-axis (Q x = -0.604); (iii) vitreous cavity depth is 17.339 mm; (iv) anterior lens radius (R = 8.22 mm); and (v) anterior lens conic constant (Q = -2.314). The model is configured to focus on a near object approximately 50 cm away from the eye. The modified myopia schematic model eye was corrected one at a time using the control (C2) contact lens and the exemplary embodiment (D2) contact lens.

[0310] The reference (C2) contact lens represents a single-view torus modeled using the following parameters: front surface (R = 8.226 mm, Q = -0.392), center thickness (0.135 mm), and rear surface of the torus (R...). y = 7.75 mm, Q y = -0.25; R x = 7.829mm, Q x = -0.604) and refractive index 1.38. The contrast contact lens C2 has no / lacks any non-refractive features contemplated in this disclosure.

[0311] The exemplary embodiment of the contact lens (D2) is a single-view torus surface having the same optical design as the reference C2. The exemplary embodiment of the contact lens (D2) is further configured with, as shown in the figure below. Figure 24 The disclosed additional non-refractive features.

[0312] The non-refractive feature of exemplary embodiment D2 includes a pattern (2403) of dots arranged in a hexagonal pattern. This random pattern (2403) is positioned within an optical region (2401) surrounding the optical center of the contact lens (2402). The total number of dots is 7. The overall diameter of the dot pattern is approximately 3.5 mm. The diameter (2404) of each dot in the dot pattern is approximately 125 μm.

[0313] For identification and readability, the non-refractive features are magnified relative to the other features of the contact lens. The remainder of the non-refractive features of the optical zone (2401) without exemplary embodiment D2 is configured with basic monocular prescription parameters that match the basic prescription of the eye.

[0314] According to the steps disclosed in paragraphs

[00271] to

[00273] , when the contact lens design of embodiment C2 and contact lens design of embodiment D2 are fitted onto the illustrative model eye of example 2, a simulated retinal image is calculated and analyzed by means of the contact lens design of embodiment C2 and contact lens design of embodiment D2.

[0315] In this Example 2, the additional variables of the virtual retina platform are conceived to have the following settings; the options for the contrast gain control mechanism described in Equations 1, 5, and 6 are used in conjunction with the following input parameter values: (i) the amplification λ of the outer mesh layer per normalized luminance unit. OPL The value is 150 Hz; (ii) Bipolar inert leakage (iii) Feedback amplification λ A The Hz value is 100 Hz; (iv) the spatial scale σA is 2.5°; and (v) the temporal scale τA is 0.01 ms. The neuron bundles (1402) are arranged in a circular pattern spanning a 15° x 15° field of view.

[0316] The sparse lateral connectivity pattern of the virtual retina was used with 10 presynaptic neurons having 10% positive weights and a weight variance of 0.01. Furthermore, the supplementary high-pass filter option for the outer reticular layer described in Equations 2 and 3 was used with the following parameter values: a time scale of 0.2 ms and a spatial scale of 0.5°. The postsynaptic pooling option was turned off.

[0317] Post-processing of the simulated retinal image calculated for the control (C2) contact lens design of Example 2 was performed using the virtual retina platform as described herein, generating a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 25 ) and the histogram of surrounding stimuli, which is a function of time, highlighting the average peak rate ( Figure 26 ). Figure 25 and Figure 26The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0318] Post-processing of the simulated retinal image calculated for the contact lens design of Example 2 (D2) using the virtual retina platform as described herein generated a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 27 The histogram of surrounding stimuli, which is highlighted as a function of time, shows the average peak rate. Figure 28 ). Figure 27 and Figure 28 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0319] For cells exhibiting two types of polarity—light-giving polarity and light-removing polarity—the description under the control (C2) contact lens condition is as follows: Figure 25 The neuronal activity of the spike sequence is either time-invariant or monotonic as a function of time. On the other hand, the description in the case of the contact lens in embodiment (D1) is as follows: Figure 26 The neuronal activity of the spike sequence is either time-varying or non-monotonic as a function of time.

[0320] In Example 2, the depiction is as follows, with reference to the (C2) contact lens. Figure 26 The average peak rate of neuronal activity follows a linear profile, except for the initial 150 milliseconds representing signal stabilization. This observed pattern is similar for cells with two types of polarity—light-giving polarity and light-removing polarity.

[0321] In Example 2, after an initial 150 ms stabilization period, the average peak rate obtained for the illuminated type of cells was approximately one-third to one-quarter the size of the average peak rate obtained for the de-illuminated type of cells, as disclosed herein.

[0322] On the other hand, in the case of contact lens in embodiment (D1), it is depicted as Figure 28 The average peak rate of neuronal activity as a function of time is either time-varying or non-monotonic. However, compared to the results obtained by implementation D1 in Example 1, the changes within the peak rate as a function of time obtained by implementation D2 in Example 2 are lower in both magnitude and frequency.

[0323] In Example 2, the average peak rate obtained by the contact lens of Embodiment (D2) for illuminated cells is at least 1.5 times that obtained by the control (D2) contact lens for illuminated cells. In this example, the average peak rate obtained by the contact lens of Embodiment (D2) for both illuminated and de-illuminated cells... Figure 28 The average peak rate depicted as a function of time follows a pattern that varies with time. The instability and nonlinearity in the peak response obtained by implementing the lens are attributed to artificial edges or luminous contrast profiles in the retinal image, or the temporal variation of the artificial edges.

[0324] In Example 2, on-axis and off-axis evaluations of optical performance were modeled in monochromatic mode (589 nm) with a pupil analysis diameter of 4 mm. As described in this paper... Figure 29 and Figure 30 The wide-area optical performance, measured using a modulation transfer function as a function of spatial frequency at a pupil diameter of 4 mm, is virtually indistinguishable between the control (C2) contact lens and the exemplary embodiment (D2) contact lens. In Example 2, for off-axis performance, a field of view of 15° is considered for performance evaluation, i.e., ±7.5° from the center.

[0325] Example 3 – Designing D3 in contrast to C3 and exemplary implementation

[0326] In this example 3, the following parameters of the illustrative model eye in Table 1 are changed to represent a 3D myopic eye in its unadapted state (i.e., the basic prescription Rx is -3D): (i) the vitreous cavity depth is 17.65 mm; and (ii) the radius of curvature is 13.5 mm.

[0327] The model is configured to focus on a distant object located approximately at optical infinity from the eye. The modified myopia model's eye model is corrected one at a time using a control (C3) contact lens and an exemplary embodiment (D3) contact lens. The control (C3) contact lens represents a single-vision lens modeled using the following parameters: anterior surface (R = 8.262 mm, Q = -0.137), center thickness (0.135 mm), posterior surface (R = 7.75 mm, Q = -0.25), and refractive index of 1.42. The control contact lens C3 has none of the non-refractive features contemplated in this disclosure.

[0328] The second lens D3 represents the following exemplary embodiment: this exemplary embodiment is also a single-view contact lens having the same parameters as the reference C3, and this exemplary embodiment is further configured with Figure 31 The non-refractive characteristics disclosed in the paper.

[0329] Exemplary Implementation Example D3 ( Figure 31 The non-refractive features of the contact lens (3102) include a random pattern (3103) formed by stripes or thickened lines, which comprises multiple stripes. This random pattern is positioned within an optical region surrounding the optical center of the optical area (3101) of the contact lens (3102). The total number of stripes is 7. The overall diameter of the grid pattern is approximately 4 mm. The size of each strip in the random strip pattern is approximately between 50 µm and 1.25 mm (3104).

[0330] For identification and readability, the non-refractive features are magnified relative to the other features of the contact lens. The remainder of the non-refractive features of the optical zone (3101), without exemplary embodiment D3, is configured with basic monocular prescription parameters that match the basic prescription of the eye.

[0331] According to the steps disclosed in paragraphs

[00271] to

[00273] , when the C3 contact lens design and the embodiment D3 contact lens design are fitted onto the illustrative model eye of Example 3, a simulated retinal image is calculated and analyzed by comparing it with the C3 contact lens design and the embodiment D3 contact lens design.

[0332] In this Example 3, the additional variables of the virtual retina platform are conceived to have the following settings; the options for the contrast gain control mechanism described in Equations 1, 5, and 6 are used in conjunction with the following input parameter values: (i) the amplification λ of the outer mesh layer per normalized luminance unit. OPL The value is 150 Hz; (ii) Bipolar inert leakage (iii) Feedback amplification λ A The Hz value is 100 Hz; (iv) the spatial scale σA is 2.5°; and (v) the temporal scale τA is 0.01 ms. The neuron bundles (1602) are arranged in a circular pattern spanning a 5° × 5° field of view. The sparse lateral connectivity pattern of the virtual retina is not used. Furthermore, the supplementary high-pass filter option for the outer reticular layer described in Equations 2 and 3 is used with the following parameter values: a temporal scale of 0.2 ms and a spatial scale of 0.5°. The postsynaptic pooling option is turned off.

[0333] Post-processing of the simulated retinal image calculated for the control (C3) contact lens design of Example 3 was performed using the virtual retina platform as described herein, generating a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 32 ) and the histogram of surrounding stimuli, which is a function of time, highlighting the average peak rate ( Figure 33 ). Figure 32 and Figure 33The top and bottom subplots represent data for the light-giving and light-removing cells, respectively. Post-processing of the simulated retinal image calculated for the contact lens design of Example 3 (D3) using the virtual retina platform as described herein generated a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 34 ) and the histogram of surrounding stimuli, which is a function of time, highlighting the average peak rate ( Figure 35 ). Figure 34 and Figure 35 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0334] For cells exhibiting two types of polarity—light-giving polarity and light-removing polarity—the following is described in the case of a control (C3) contact lens: Figure 32 The neuronal activity of the spike sequence, as a function of time, is relatively constant or exhibits very small variations or fluctuations. On the other hand, the depiction in the case of the contact lens in embodiment (D1) is as follows: Figure 34 The neuronal activity of the spike sequence as a function of time is relatively variable or has large variations or fluctuations over time.

[0335] In Example 3, the depiction is as follows, with reference to the (C3) contact lens. Figure 33 The average peak rate of neuronal activity follows a relatively monotonous profile after the initial 100 ms representing signal stabilization. This observed pattern is similar for cells with two types of polarity—light-giving polarity and light-removing polarity. In Example 3, excluding the initial 100 ms stabilization period, the average peak rate for light-giving cells in the case of the control (C3) contact lens is approximately four times larger than the average peak rate obtained in the case of light-removing cells, as disclosed herein.

[0336] On the other hand, the description in the case of contact lens in embodiment (D3) is as follows Figure 34 The average peak rate of neuronal activity as a function of time is either time-varying or non-monotonic. In this Example 3, for both illuminated and deiled cells, the cumulative average peak rate as a function of time obtained by Implementation D3 is lower than the results obtained by Control C3 in Example 3.

[0337] The instability and nonlinearity in the peak response obtained by implementing the lens are attributed to artificial edges or luminous contrast profiles in the retinal image, or the temporal variation of artificial edges.

[0338] In this example, the contact lens obtained by embodiment (D2) is used for both light-providing and light-removing cells. Figure 28 The average peak rate depicted as a function of time follows a pattern that varies with time. Although the control lens (C3) in Example 3... Figure 33 Both the average peak rate of the light-giving type and the average peak rate of the light-removing type depicted in the figure show some changes over time, but the time change observed in the average peak rate obtained by the contact lens of embodiment (D3) is much greater than that of the control (C3) contact lens.

[0339] In this Example 3, under photopic vision conditions and with a pupil analysis diameter of 6 mm, the on-axis and off-axis evaluations of optical performance are modeled using a photometric function describing the average spectral sensitivity of human visual perception of brightness in a multicolor mode spanning 470 nm to 650 nm.

[0340] In this example, for simplicity, the photoreceptor density, as a function of retinal eccentricity, is kept constant; however, other variations of the retinal model involving changes in photoreceptor density can be envisioned.

[0341] As in this article Figure 36 and Figure 37 The wide-area optical performance, measured using a modulation transfer function as a function of spatial frequency at a pupil diameter of 6 mm, is virtually indistinguishable between the control (C3) contact lens and the exemplary embodiment (D3) contact lens. In Example 3, for off-axis performance, a field of view of 5° is considered for performance evaluation, i.e., ±2.5° from the center.

[0342] Example 4 – Designing D4 in contrast to C4 and exemplary implementation

[0343] In this Example 4, the following parameters of the illustrative model eye in Table 1 are changed to represent a 3D myopic eye in its unadapted state (i.e., the basic prescription Rx is -3D): (i) the vitreous cavity depth is 17.65 mm; and (ii) the retinal curvature radius is 13.5 mm. The model is configured to focus on an object located approximately at optical infinity from the eye.

[0344] The modified myopia model eye model is corrected one at a time using the contrast (C4) contact lens and the exemplary embodiment (D4) contact lens. The contrast (C4) contact lens represents a single-vision lens modeled using the following parameters: anterior surface (R = 8.262 mm, Q = -0.137), central thickness (0.135 mm), posterior surface (R = 7.75 mm, Q = -0.25), and refractive index of 1.42. The contrast contact lens C4 has no / lacks any non-refractive features contemplated in this disclosure.

[0345] The second lens D4 represents the following exemplary embodiment: this exemplary embodiment is also a single-view contact lens having the same parameters as the reference C4, and this exemplary embodiment is further configured with Figure 38 The non-refractive characteristics disclosed in the paper.

[0346] The non-refractive feature of Exemplary Implementation Example D4 includes a grid pattern (3803) having multiple linear or striped features. This grid pattern (3803) is positioned within an optical region surrounding the optical center of the optical zone (3801) of the contact lens (3802). The total number of linear or striped features is six, three horizontally and three vertically. The overall diameter of the grid pattern is approximately 3 mm. The size of each line or stripe in the grid pattern is approximately between 75 µm and 1 mm (3804). For identification and readability, the non-refractive feature is magnified relative to other features of the contact lens. The remainder of the non-refractive feature of the optical zone (3801) without Exemplary Implementation D4 is configured with basic monocular prescription parameters matching the basic prescription of the eye.

[0347] According to the steps disclosed in paragraphs

[00271] to

[00273] , when the C4 contact lens design and the D4 contact lens design are fitted onto the illustrative model eye of Example 4, a simulated retinal image is calculated and analyzed by comparing it with the C4 contact lens design and the D4 contact lens design.

[0348] In this Example 4, additional variables for the virtual retina platform are envisioned to have the following settings: the option for the contrast gain control mechanism described in Equations 1, 5, and 6 is disabled. The neuron bundles (1602) are arranged in a circular pattern spanning a 15° × 15° field of view. The sparse lateral connectivity pattern of the virtual retina is not used.

[0349] Additionally, the supplementary high-pass filter option for the outer mesh layer described in Equations 2 and 3 is disabled. The postsynaptic pooling option is also disabled.

[0350] Post-processing of the simulated retinal image calculated from the control (C4) contact lens design of Example 4 was performed using the virtual retina platform as described herein, generating a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 39 ) and the histogram of surrounding stimuli, which is a function of time, highlighting the average peak rate ( Figure 40 ). Figure 39 and Figure 40 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0351] Post-processing of the simulated retinal image calculated for the contact lens design of Example 4 (D4) using the virtual retina platform as described herein generated a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 41 ) and the histogram of surrounding stimuli, which is a function of time, highlighting the average peak rate ( Figure 42 ). Figure 41 and Figure 42 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0352] For cells with two types of polarity—light-giving polarity and light-removing polarity—the description in the case of control (C4) contact lens is as follows: Figure 39 The neuronal activity of the spike sequence, as a function of time, is relatively constant over time or exhibits very small changes or fluctuations. On the other hand, the depiction in the case of the contact lens in embodiment (D4) is as follows: Figure 41 The neuronal activity of the spike sequence as a function of time is relatively variable or has large variations or fluctuations over time.

[0353] In Example 4, the depiction is as follows, with reference to the (C4) contact lens. Figure 40 The average peak rate of neuronal activity follows a relatively monotonous profile after the initial 100 milliseconds representing signal stabilization. This observed pattern is similar for cells with two types of polarity—light-giving polarity and light-removing polarity.

[0354] In Example 4, excluding the initial 100 ms stabilization period, the average peak rate for light-exposed cells in the case of the control (C4) contact lens was approximately twice the average peak rate obtained in the case of light-deprived cells, as disclosed herein.

[0355] On the other hand, the depiction in the case of contact lens in embodiment (D4) is as follows Figure 41 The average peak rate of neuronal activity as a function of time varies over time.

[0356] In this example, for both light-giving and light-removing cells, the contact lens obtained through implementation (D4) Figure 42 The average peak rate depicted as a function of time follows a time-varying pattern. The magnitude or size of the time-varying pattern observed within the average peak rate obtained by the contact lens of embodiment (D4) is smaller than that of other contact lenses of this disclosure.

[0357] In Example 4, on-axis and off-axis evaluations of optical performance are modeled in monochromatic mode (589 nm) and at a pupil analysis diameter of 4 mm. As in this paper... Figure 43 and Figure 44 The wide-area optical performance, as depicted and measured using a modulation transfer function as a function of spatial frequency at a pupil diameter of 6 mm, is virtually indistinguishable between the control (C4) contact lens and the exemplary embodiment (D4) contact lens. In Example 4, for off-axis performance, a field of view of 15° is considered for performance evaluation, i.e., ±7.5° from the center.

[0358] Example 5 – Designing D5 in contrast to C5 and exemplary implementation

[0359] In this Example 5, the following parameters of the schematic model eye in Table 1 are changed to represent a 3D myopic eye (Rx: -3D) in its 1D adaptation state: (i) vitreous cavity depth of 17.65 mm; (ii) retinal curvature radius of 13.5 mm; and (iii) anterior lens radius (R = 9.081 mm) and conic constant (Q = -4.123).

[0360] The model is configured to focus on a near object approximately 1 meter from the eyes. The modified myopia schematic model eye is corrected one at a time using a control (C5) contact lens and an exemplary embodiment (D5) contact lens.

[0361] The contrast (C5) contact lens represents a single-view lens modeled using the following parameters: front surface (R = 8.262 mm, Q = -0.137), center thickness (0.135 mm), rear surface (R = 7.75 mm, Q = -0.25), and refractive index of 1.42. The contrast contact lens C5 has none of the non-refractive features envisioned in this disclosure.

[0362] The second lens D5 represents the following exemplary embodiment: this exemplary embodiment is also a single-view contact lens having the same parameters as the reference C5, and this exemplary embodiment is further configured with Figure 45 The non-refractive characteristics disclosed in the paper.

[0363] Exemplary Implementation D5 ( Figure 45 The non-refractive features of the contact lens (4502) include a spoke pattern (4503) with multiple linear features. This spoke pattern (4503) is positioned within the optical zone (4501) of the contact lens (4502). The total number of spoke features is 8. The overall diameter of the spoke pattern is approximately 4 mm. The size of each line in the spoke pattern is approximately between 100 μm and 1 mm (4504).

[0364] For identification and readability, the non-refractive features are magnified relative to the other features of the contact lens. The remainder of the non-refractive features of the optical zone (4501), without exemplary embodiment D5, is configured with basic monocular prescription parameters that match the basic prescription of the eye.

[0365] According to the steps disclosed in paragraphs

[00271] to

[00273] , when the C5 contact lens design and the D5 contact lens design are fitted onto the illustrative model eye of Example 5, a simulated retinal image is calculated and analyzed by comparing it with the C5 contact lens design and the D5 contact lens design.

[0366] In this Example 5, the additional variables of the virtual retina platform are conceived to have the following settings; the options for the contrast gain control mechanism described in Equations 1, 5, and 6 are used in conjunction with the following input parameter values: (i) the amplification λ of the outer mesh layer per normalized luminance unit. OPL The value is 150 Hz; (ii) Bipolar inert leakage (iii) Feedback amplification λ A The Hz value is 100 Hz; (iv) the spatial scale σA is 2.5°; and (v) the temporal scale τA is 0.01 ms. The neuron bundles (1602) are arranged in a circular pattern spanning a 5° × 5° field of view. The sparse lateral connectivity pattern of the virtual retina is not used. In addition, the supplementary high-pass filter option for the outer reticular layer described in Equations 2 and 3 is turned off. The postsynaptic pooling option is also turned off.

[0367] Post-processing of the calculated simulated retinal image of the control (C5) contact lens design of Example 5 was performed using the virtual retina platform as described herein, generating a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 46 ) and the histogram of surrounding stimuli, which is a function of time, highlighting the average peak rate ( Figure 47 ). Figure 46 and Figure 47The top and bottom subplots represent data for the light-giving and light-removing cells, respectively. Post-processing of the simulated retinal image calculated for the contact lens design of Example 5 (D5) using the virtual retina platform as described herein generated a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 48 ) and the histogram of surrounding stimuli, which is a function of time, highlighting the average peak rate ( Figure 49 ). Figure 48 and Figure 49 The top and bottom subplots represent data for light-giving and light-removing cells, respectively. For cells with two types of polarity—light-giving and light-removing polarity—the depiction in the case of control (C5) contact lens is as follows. Figure 46 The neuronal activity of the spike sequence, as a function of time, is relatively constant over time or exhibits very small changes or fluctuations. On the other hand, the depiction in the case of the contact lens in embodiment (D5) is as follows: Figure 48 The neuronal activity of the spike sequence as a function of time is relatively time-varying and monotonically decreases or increases.

[0368] In Example 5, the depiction is as follows, in the case of the contact lens (C5) Figure 47 The average peak rate of neuronal activity follows a relatively monotonous profile after the initial 100 ms representing signal stabilization. This observed pattern is similar for cells with two types of polarity—light-giving polarity and light-removing polarity. In Example 5, excluding the initial 100 ms stabilization period, the average peak rate for light-giving cells in the case of the control (C5) contact lens is approximately three times larger in magnitude than the average peak rate obtained in the case of light-removing cells, as disclosed herein.

[0369] On the other hand, the description in the case of contact lens in embodiment (D5) is as follows Figure 49 The average peak rate of neuronal activity as a function of time varies over time. In this example, for both illuminated and de-illuminated cells, the results obtained via the contact lens in embodiment (D5) are... Figure 49 The average peak rate, as a function of time, depicted in the image follows a time-varying pattern. The instability and nonlinearity in the peak response obtained by implementing the lens are attributed to artificial edges or luminous contrast profiles in the retinal image, or the temporal variation of the artificial edges.

[0370] In Example 5, under photopic vision conditions and with a pupil analysis diameter of 5 mm, the on-axis and off-axis evaluations of optical performance are modeled in multicolor mode using a photometric function that describes the average spectral sensitivity of human visual perception of brightness.

[0371] As in this article Figure 50 and Figure 51 The wide-area optical performance, measured using a modulation transfer function as a function of spatial frequency at a pupil diameter of 5 mm, is remarkably similar between the control (C5) contact lens and the exemplary embodiment (D5) contact lens, i.e., the area below the curve represented by the solid black line and the area below the curve represented by the dashed black line have a variation of less than 5%. In Example 5, for off-axis performance, a field of view of 15° is considered for performance evaluation, i.e., ±7.5° from the center.

[0372] Example 6 – Designing D6 in contrast to C6 and exemplary implementation

[0373] In this Example 6, the following parameters of the illustrative model eye in Table 1 are changed to represent a 4D myopic eye in its 2D adaptation state (i.e., the basic prescription Rx is -4D): (i) the vitreous cavity depth is 18.04 mm; (ii) the retinal curvature radius is 13.5 mm; and (iii) the anterior lens radius (R = 7.794 mm) and conic constant (Q = -3.959) parameters.

[0374] The model is configured to focus on a near object approximately 50 cm from the eye. The modified schematic model eye of myopia is corrected one at a time using a control (C6) contact lens and an exemplary embodiment (D6) contact lens. The control (C6) contact lens represents a single-vision lens modeled using the following parameters: anterior surface (R = 8.41 mm, Q = -0.112), central thickness (0.135 mm), posterior surface (R = 7.75 mm, Q = -0.25), and refractive index of 1.42. The control contact lens C6 has none of / lacks any of the non-refractive features contemplated in this disclosure.

[0375] The second lens D6 represents the following exemplary embodiment: this exemplary embodiment is also a single-view contact lens having the same parameters as the reference C6, and this exemplary embodiment is further configured with Figure 52 The non-refractive characteristics disclosed in the paper.

[0376] The non-refractive feature of Example D6 in the exemplary embodiment includes a random pattern (5203) comprising a plurality of elliptical dot features slightly stretched in the horizontal direction. This random pattern is positioned within an optical region (5201) surrounding the optical center of the contact lens (5202) of the exemplary embodiment. The total number of elliptical dot features in (5202) is 18. The overall diameter of the random pattern is approximately 3 mm. The size of each elliptical dot feature is approximately between 125 μm and 200 μm (5204).

[0377] For identification and readability, the non-refractive features are magnified relative to the other features of the contact lens. The remainder of the non-refractive features of the optical zone (5201), without exemplary embodiment D6, is configured with basic monocular prescription parameters that match the basic prescription of the eye.

[0378] According to the steps disclosed in paragraphs

[00271] to

[00273] , a simulated retinal image is calculated and analyzed by comparing the C6 contact lens design and the D6 contact lens design when fitted onto the illustrative model eye of Example 6. In this Example 6, additional variables of the virtual retinal platform are conceived to have the following settings: the option of the contrast gain control mechanism described in Equations 1, 5, and 6 is turned off. The arrangement of the neuron bundles (1602) is a circular arrangement spanning a 15° × 15° field of view.

[0379] The sparse lateral connectivity pattern of the virtual retina was used with 10 presynaptic neurons with 10% positive weights and a weight variance of 0.01. The supplementary high-pass filter option for the outer reticular layer described in Equations 2 and 3 was turned off. The postsynaptic pooling option was also turned off.

[0380] Post-processing of the simulated retinal image calculated from the control (C6) contact lens design of Example 6 was performed using the virtual retina platform as described herein, generating a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 53 ) and the histogram of surrounding stimuli, which is a function of time, highlighting the average peak rate ( Figure 54 ). Figure 53 and Figure 54 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0381] Post-processing of the simulated retinal image calculated for the contact lens design of Example 6 (D6) using the virtual retina platform as described herein generates a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 55 The histogram of surrounding stimuli, which is highlighted as a function of time, shows the average peak rate. Figure 56 ). Figure 55 and Figure 56 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0382] For cells exhibiting two types of polarity—light-giving polarity and light-removing polarity—the description under control (C6) contact lens conditions is as follows: Figure 53The neuronal activity of the spike sequence, as a function of time, is relatively constant over time or exhibits very small changes or fluctuations. On the other hand, the depiction in the case of the contact lens in embodiment (D6) is as follows: Figure 55 The neuronal activity of the spike sequence, as a function of time, is relatively time-varying and monotonically decreases or increases. The instability and nonlinearity in the spike response obtained by implementing the lens are attributed to artificial edges or luminous contrast contours in the retinal image, or the temporal variation of the artificial edges.

[0383] In Example 6, the depiction is as follows in the case of the contact lens (C6): Figure 54 The average peak rate of neuronal activity follows a relatively monotonous profile after the initial 100 ms representing signal stabilization. This observed pattern is similar for cells with two types of polarity—light-giving polarity and light-removing polarity. In Example 6, excluding the initial 100 ms stabilization period, the average peak rate for light-giving cells in the case of the control (C6) contact lens is approximately three times larger in magnitude than the average peak rate obtained in the case of light-removing cells, as disclosed herein.

[0384] On the other hand, the description in the case of contact lens in embodiment (D6) is as follows Figure 56 The average peak rate of neuronal activity as a function of time varies over time. In this example, for both illuminated and deiled cells, the contact lens obtained via embodiment (D6) is used. Figure 56 The average peak rate depicted as a function of time follows a pattern that varies with time.

[0385] In this example 6, on-axis and off-axis evaluations of optical performance are modeled in monochromatic mode (589 nm) and at a pupil analysis diameter of 4 mm.

[0386] As in this article Figure 57 and Figure 58 The wide-area optical performance measured using the modulation transfer function as a function of spatial frequency at a pupil diameter of 4 mm is virtually indistinguishable between the control (C6) contact lens (represented by the solid black line) and the exemplary embodiment (D6) contact lens (represented by the dashed black line). In Example 6, for off-axis performance, the field of view considered for performance evaluation is 15°, i.e., ±7.5° from the center.

[0387] Example 7 – Designing D7 in contrast to C7 and exemplary implementation

[0388] In Example 7, the following parameters of the schematic model eye in Table 1 are modified to represent a 4D myopic eye in its unadapted state (i.e., the basic prescription Rx is -4D): (i) the vitreous cavity depth of the eye is 18.04 mm; (ii) the retinal curvature radius is 13.5 mm. The model is configured to focus on a distant object located approximately at optical infinity from the eye. The modified schematic model eye of myopia is corrected one at a time by a control (C7) contact lens and an exemplary embodiment (D7) contact lens. The control (C7) contact lens represents a single-vision lens modeled using the following parameters: anterior surface (R = 8.41 mm, Q = -0.112), central thickness (0.135 mm), posterior surface (R = 7.75 mm, Q = -0.25), and refractive index of 1.42. The control contact lens C7 has no / lacks any of the non-refractive features contemplated in this disclosure. The second lens D7 represents the following exemplary embodiment: this exemplary embodiment is also a single-view contact lens having the same parameters as the reference C7, and this exemplary embodiment is further configured with Figure 59 The non-refractive characteristics disclosed in the paper.

[0389] The non-refractive feature of the exemplary embodiment D7 includes a spiral pattern (5903) with multiple dot-like features. This spiral pattern is positioned within the optical region (5901) of the contact lens (5902). The total number of dot-like features in each arm is 49. The overall diameter of the spiral pattern is approximately 6 mm. The width of each dot-like feature is approximately between 125 μm (5904). For identification and legibility, the non-refractive feature is magnified relative to other features of the contact lens. The remainder of the non-refractive feature in the optical region (5901) without the exemplary embodiment D7 is configured with basic monocular prescription parameters matching the basic prescription of the eye.

[0390] According to the steps disclosed in paragraphs

[00271] to

[00273] , when the contact lens design of embodiment C7 and contact lens design of embodiment D7 are fitted onto the illustrative model eye of example 7, a simulated retinal image is calculated and analyzed by means of the contact lens design of embodiment C7 and contact lens design of embodiment D7.

[0391] In this Example 7, the additional variables of the virtual retina platform are conceived to have the following settings; the options for the contrast gain control mechanism described in Equations 1, 5, and 6 are used in conjunction with the following input parameter values: (i) the amplification λ of the outer mesh layer per normalized luminance unit. OPL The value is 150 Hz; (ii) Bipolar inert leakage (iii) Feedback amplification λ AThe Hz was 100 Hz; (iv) the spatial scale σA was 2.5°; and (v) the temporal scale τA was 0.01 ms. The neuronal bundles (1602) were arranged in a circular pattern spanning a 5° × 5° field of view. The sparse lateral connectivity pattern of the virtual retina was turned off. The supplementary high-pass filter option for the outer retina described in Equations 2 and 3 was turned off. The postsynaptic pooling option was also turned off. The simulated retinal image calculated from the control (C7) contact lens design of Example 7 was post-processed using the virtual retina platform as described herein, generating a spike sequence as a function of time for cells with both light-giving and light-removing polarities. Figure 60 ) and the histogram of surrounding stimuli, which is a function of time, highlighting the average peak rate ( Figure 61 ). Figure 60 and Figure 61 The top and bottom subplots represent data for the light-giving and light-removing cells, respectively. Post-processing of the simulated retinal image calculated for the contact lens design of Example 7 (D7) using the virtual retina platform as described herein generated a sequence of spikes as a function of time for cells with both light-giving and light-removing polarities. Figure 62 ) and the histogram of surrounding stimuli, which is a function of time, highlighting the average peak rate ( Figure 63 ). Figure 62 and Figure 63 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0392] For cells with two types of polarity—light-giving polarity and light-removing polarity—the description in the case of control (C7) contact lens is as follows: Figure 60 The neuronal activity of the spike sequence, as a function of time, is relatively constant over time or exhibits very small changes or fluctuations. On the other hand, the depiction in the case of the contact lens in embodiment (D7) is as follows: Figure 62 The neuronal activity of the spike sequence is relatively time-varying as a function of time and fluctuates with varying periodicity.

[0393] In Example 7, the depiction is as follows in the case of the contact lens (C7). Figure 61 The average peak rate of neuronal activity follows a relatively monotonous profile after the initial 100 milliseconds representing signal stabilization. This observed pattern is similar for cells with two types of memory—light-giving polarity and light-removing polarity.

[0394] On the other hand, the depiction in the case of contact lens in embodiment (D7) is as follows Figure 62The average peak rate of neuronal activity as a function of time varies over time. In this example, for both illuminated and deiled cells, the results obtained via the contact lens in embodiment (D7) are... Figure 63 The average peak rate depicted as a function of time follows a pattern that varies with time.

[0395] In Example 7, on-axis and off-axis evaluations of optical performance are modeled in monochromatic mode (589 nm) at a pupil analysis diameter of 6 mm. As described in this paper... Figure 64 and Figure 65 The wide-area optical performance, measured using a modulation transfer function as a function of spatial frequency at a pupil diameter of 6 mm, is virtually indistinguishable between the control (C7) contact lens (represented by a solid black line) and the exemplary embodiment (D7) contact lens (represented by a dashed black line).

[0396] In Example 7, for off-axis performance, a field of view of 15° is considered for performance evaluation, i.e., ±7.5° from the center. The simulation technique described herein is one of many methods used to demonstrate that a single-vision contact lens with the envisioned non-refractive features disclosed herein provides an increase in retinal ganglion cell activity compared to a standard care single-vision contact lens.

[0397] Implementation of eyeglass lens

[0398] Modeling of various spectacle lens implementations demonstrates that non-refractive features used in conjunction with a single-vision optical profile provide an increase in retinal ganglion cell activity, which is measured, alternatively, by measuring an increase in the average retinal ganglion cell peak rate obtained using a virtual retinal platform simulating the performance of the wearer's eye.

[0399] Figure 66A non-scale front view of a prior art spectacle lens (6601) and an exemplary spectacle lens (6602) is shown. The spectacle lens measures approximately 40 mm × 50 mm. In both cases, the entire spectacle lens area constitutes the optical zone of the spectacle lens. The spectacle lens embodiment (6602) is configured with a non-refractive feature (6603) comprising a grid pattern consisting of four horizontal lines or stripes and four vertical lines or stripes. The optical zone is designed generally around an optical center (6605) to have a single-vision refractive capability matching the basic prescription of the eye. The grid pattern, located at the center of the spectacle lens embodiment, spans approximately 25 mm in height and width. The boundaries (6603) of these grid lines are configured to be completely opaque or substantially opaque. The width (6604) of the non-refractive feature is approximately between 50 μm and 100 μm, and is only magnified in the figures to show its characteristic relative to the size of the contact lens described herein. Figure 66 The implementation can also be configured in other variations, for example, the width of the envisioned non-refractive design feature within the optical region can be at least 125 μm, 150 μm, 175 μm, 200 μm or 250 μm. Figure 66 The implementation can also be configured in other variations. For example, the envisioned non-refractive design features may include random patterns, multiple circles, ellipses, triangles, rectangles, hexagons, regular polygons, or irregular polygons; wherein the width defining the boundaries of the multiple apertures may be between 50 μm and 125 μm, between 150 μm and 250 μm, or between 100 μm and 300 μm. Figure 66 In a preferred variation of the implementation, the maximum width of the non-refractive feature, i.e., the width of the lines forming the grid pattern or any other pattern, does not exceed 150 μm, 200 μm, or 250 μm, to avoid any unnecessary impact on the resolution characteristics of the wearer's eye. In other embodiments, the envisioned non-refractive feature may be positioned at the periphery of the optical zone of the eyeglass design. In yet another eyeglass lens embodiment, the number of fine lines or stripes forming the grid pattern may be at least 5, 9, 15, or 25. In some other eyeglass lens embodiments, the design feature, the number of lines or stripes forming the grid pattern, may be between 5 and 9, or between 9 and 15, or between 9 and 15, or between 5 and 25. In another embodiment, a single, generally uninterrupted long curve or zigzag line with a length of at least 3 mm, 6 mm, 9 mm, or 12 mm passing through the optical zone is conceivable.

[0400] In another embodiment of the spectacle lens, one or more stripes can be arranged symmetrically or randomly, and these stripes can be positioned concentrically with the optical axis or off-center relative to the optical center. The stripes can also be composed of straight lines or curves, and they can contact or intersect each other, or be arranged entirely separately, or a combination of the foregoing. The stripes can vary in width and length. Lenses worn in the left and right eyes can have different patterns.

[0401] In yet another embodiment of the spectacle lens, the envisioned design features (i.e., multiple stripes or moiré patterns) can be separated from each other within the spectacle lens. In yet another embodiment, the envisioned multiple non-refractive features can be configured to be adjacent to or interleaved with each other.

[0402] The natural eye movements of eyeglass wearers may result in temporally varying stimuli, which can further increase the inhomogeneity artificially introduced into the visual image. This, in turn, can enhance the efficacy of treatments for the wearer, for example, thereby reducing the rate of myopia progression in the wearer to a greater extent. Figure 67 A schematic diagram depicts incident light entering a 2D myopic model eye (6700) from a wide-angle field of view (6701) with a convergence / divergence of 0D at a visible wavelength, such as 555 nm, corrected using a standard single-vision lens (6702) of the prior art. Retinal ganglion cell activity is recorded by an on-center / off-periphery circuit and an off-center / on-periphery circuit (6703). The capture of retinal ganglion cell activity at the retinal plane using a standard single-vision lens (6702) is induced by simulating habitual saccadic eye movements to illustrate minimum retinal activity, or retinal activity at the baseline rate, or minimum temporal variation of retinal activity. The relative difference in the time integrals of on-field and off-field activity determines further eye growth.

[0403] This disclosure presupposes that an inactive retina triggers eye growth, while an active retina slows growth or triggers a stop signal. This disclosure further envisions that standard single-vision lenses or spectacle lenses of the prior art, and / or spatially uniform visual images, contribute to the production of uniform and spatially largely borderless visual images, thereby keeping the retina in a baseline state (i.e., the baseline or constant firing pattern of retinal ganglion cells), and thus promoting further eye growth, resulting in greater myopia.

[0404] Figure 68A schematic diagram is shown depicting incident light entering a 2D myopia model eye (6800) from a wide field of view (6801) with a convergence of 0 D at a visible wavelength, such as 555 nm, which is corrected by a spectacle implementation (6802). Retinal ganglion cell activity at the retinal plane is captured by simulating habitual saccadic eye movements, using the standard spectacle implementation (6802), recorded by the light-on-center / light-off-periphery circuit and the light-off-center / light-on-periphery loop (6803), to illustrate or demonstrate increased activity at the retina compared to a baseline state.

[0405] For illustrative purposes, in Figure 67 and Figure 68 A simple model eye has been chosen in this embodiment; however, in other embodiments, illustrative ray-tracing model eyes such as those of Liou-Brennan and Escudero-Navarro can be used instead. The examples provided herein have used a 2D myopic model eye to disclose the invention; however, this disclosure can be extended to other degrees of myopia, namely -1D, -3D, -5D, or -6D. Furthermore, it should be understood that this can be extended to eyes with varying degrees of combined myopia and astigmatism. In the embodiments, the specific wavelength of 555 nm is mentioned; however, it should be understood that this can be extended to other visible wavelengths between 420 nm and 760 nm.

[0406] Modeling of various exemplary spectacle lens implementations (D8 to D10) demonstrates that the envisioned non-refractive features used in conjunction with a single-vision design provide an increase in retinal ganglion cell activity, measured by an increase in the average retinal spike rate obtained using the virtual retina platform disclosed herein. In other implementations, various other alternative measurements of retinal ganglion cell activity may be considered, for example, examining spike sequence analysis for selected neuronal bundles.

[0407] To illustrate the operation of the spectacle lens implementation according to this disclosure, improved optical modeling experiments were conducted using two different types of spectacle for each test case described herein (i.e., Examples 8 to 10).

[0408] The first type includes monocular lenses (C8 to C10), which are matched with the basic prescription of the schematic model eye to provide correction of refractive errors, thereby simulating standard treatment.

[0409] The second type includes various exemplary spectacle lens embodiments (D8 to D10) that are substantially identical to the control spectacle lenses (C8 to C10) for standard treatment of monocular vision, further configured with additional non-refractive features designed according to the invention. To illustrate the operation of the invention, the control (C8 to C10) and exemplary embodiment spectacle lenses (D8 to D10) are configured, tested / evaluated one at a time on the modified schematic model eye described in Examples 8 to 10. The surface transmittance properties of the anterior surface of the spectacle lens are modified to design the features of Examples 8 to 10. Transmittance is calculated as a fraction of 100%, where 100% means that all light is transmitted as if there were no absorption, reflection, or vignetting loss. In some embodiments of this disclosure, surface transmittance is defined as a relatively arbitrary percentage of the intensity of rays transmitted through the surface. In some other embodiments of this disclosure, the relatively arbitrary percentage of intensity may be configured to be wavelength-dependent. In some other embodiments of this disclosure, the relatively arbitrary percentage of intensity may be configured to be polarity-sensitive. To evaluate the simulated retinal ganglion cell activity, the spectacle lens was decentered relative to the optical axis of the model eye at various off-center locations to simulate saccadic eye movements. The motion of the spectacle lens relative to the optical center of the model eye was within ±5 mm in the horizontal direction. Wide-area retinal image simulation was performed at each off-center spectacle position. One hundred and one (101) such simulated retinal images constituted the input stream for the virtual retinal platform to elicit retinal ganglion cell activity. In this example, each of the 101 image frames was configured for 50 milliseconds, equivalent to a real-time stimulus presentation of 5.05 seconds for the virtual retinal model. Each frame of the input stream was configured to exceed 512 × 512 pixels, wherein each frame was configured to cover the full diameter of the circular neuronal region, thereby surrounding an approximately 15° × 15° (macula) or 20° × 20° (perima) region of the retina of the virtual retinal platform. The bit depth for each pixel in the input stream was digitized to a range from 0 to 255 (i.e., 8 bits). The specific retinal setup and configuration described in Equations 1 to 9 for demonstrating the operation of the contact lens implementation of this disclosure will be discussed in the following sections.

[0410] In all Examples 8 through 10, the outer mesh layer is configured with a central region facing approximately 1.5° (i.e., σC in Equation 2) and a surrounding region facing approximately 4.75° (i.e., σS in Equation 3). The center and surrounding time scales of the outer mesh layer are set to approximately 1 millisecond, and are represented by the variables τC and τS in Equations 2 and 3, respectively. As described in Equation 1 of this paper, the variable controlling the integration center-surrounding signal is selected as w. OPL =1 and λOPL =10. The static nonlinear coefficients of bipolar cell and ganglion cell synapses are fixed in all Examples 8 through 10. The bipolar linear threshold is set to 0, the linear threshold is kept constant at 80, and the bipolar amplification value is kept at 100. The values ​​of the neuron model are maintained in all Examples 8 through 10, where, for the simulations of Examples 8 through 10, the leakage is 0.75, the neuronal noise is 20, the membrane capacitance is 150, and the firing threshold is 2.4. The postsynaptic pooling variable σ is ignored. In Examples 8 through 10, the options for the contrast gain control mechanism, the utility of the supplementary high-pass filter of the outer reticular layer, and the utility of lateral connectivity without long-processed cells remain variable. Further details of the specific settings used are disclosed herein.

[0411] For each exemplary embodiment described herein, advanced optical modeling experiments were conducted using the following two types of spectacle lenses: (1) a single-vision lens that matches the basic prescription of the schematic model eye to provide correction of refractive errors, which simulates standard treatment; and (2) the same standard single-vision lens described above with additional non-refractive features designed according to the invention to provide increased retinal ganglion cell activity compared to the standard treatment single-vision lens.

[0412] In some implementations of spectacle lenses, the width of the opaque, semi-transparent, or absorbing boundary of the envisioned design feature (i.e., aperture) within the optical region of the spectacle lens can be at least 15 μm, 25 μm, 35 μm, 50 μm, 75 μm, 100 μm, 150 μm, 200 μm, or 250 μm.

[0413] In some spectacle lens implementations, the width of the opaque, semi-transparent, or absorbing boundary of the envisioned design feature (i.e., the aperture) within the optical zone of the spectacle lens can be configured to be no greater than 300 μm, 325 μm, 350 μm, 375 μm, or 400 μm to avoid potential degradation of the resolving power of the corrected eye and / or to maintain sufficient light transmittance under all observation conditions, such as to accommodate normal pupillary variations between 2 mm and 7 mm, covering dim lighting conditions, ambient lighting conditions, and high-level lighting conditions that the wearer may experience.

[0414] Due to the aesthetic appearance of spectacle lenses, translucent or absorbing / coloring boundaries are preferred as design features compared to opaque boundaries. In some spectacle lens embodiments, the width of the translucent boundary of the envisioned design feature on the spectacle lens can be between 15 μm and 30 μm, 25 μm and 50 μm, or 30 μm and 75 μm, or 15 μm and 100 μm. In some embodiments, the width of the design feature may not be constant across multiple apertures.

[0415] In another embodiment of the glasses, the envisioned plurality of apertures within the optical zone can only be used when the wearer is performing a specific near-vision task, such as reading, writing, playing video games, using a mobile phone, using a tablet, or using a computer.

[0416] Regarding the implementation of the envisioned design features in eyeglass lenses, in some embodiments, multiple boundaries can be introduced using materials that can be polarization-sensitive. Using such polarization-sensitive materials can enhance the wearer's aesthetics and also provide the desired edge effect to offer a stopping signal. When using multiple apertures configured with polarization-sensitive materials, selective testing scenarios (using liquid crystal displays (LCDs) or light-emitting diode displays) are conceivable.

[0417] Example 8 – Comparison (C8) Design and Exemplary Implementation (D8) Design

[0418] In this Example 8, the following parameters of the illustrative model eye in Table 1 are changed to represent a 3D myopic eye in its unadapted state (i.e., the basic prescription Rx is -3D): (i) the vitreous cavity depth of the eye is 17.63 mm; and (ii) the retinal curvature radius is 13.5 mm.

[0419] The model is configured to focus on a distant object at optical infinity from the eye. The modified myopia schematic model eye is corrected one at a time using a control (C8) spectacle lens and an exemplary embodiment (D8) spectacle lens. The control (C8) spectacle lens represents a single-vision lens modeled using the following parameters: anterior surface area (R = 2000 mm), center thickness (1.5 mm), posterior surface area (R = 144.2 mm), and refractive index of 1.5, with a total blank diameter of 50 mm. The control spectacle lens C8 has no / lacks any non-refractive features contemplated in this disclosure. The second lens D8 represents the following exemplary embodiment: this exemplary embodiment is also a single-vision spectacle lens with the same parameters as the control C8, and this exemplary embodiment is further configured with… Figure 69The non-refractive features disclosed in the embodiments. The non-refractive feature of Exemplary Implementation D8 (6900) includes a vortex pattern (6902) with six arms, each arm further including a plurality of dot features. The vortex pattern is positioned around the optical center of the spectacle lens (6901). The total number of dot features in each arm (6902) is approximately 10. The overall size of the vortex pattern is approximately 5 mm in diameter. The width of the dot features is approximately between 75 μm (6904). The remainder (6905) of Exemplary Implementation D8 is configured with single-vision parameters matching the basic prescription of the eye. The non-refractive feature of Exemplary Implementation D8 is configured such that it absorbs at least 90% of the light incident on the non-refractive feature. Following the steps disclosed in paragraphs

[00385] to

[00387] , when the spectacle design of Embodiment C8 and the spectacle design of Embodiment D8 are fitted on the illustrative model eye of Example 8, a simulated retinal image is calculated and analyzed by comparison with the spectacle design of Embodiment C8 and the spectacle design of Embodiment D8.

[0420] In this example 8, the additional variables of the virtual retina platform are conceived to have the following settings; the options of the contrast gain control mechanism described in Equations 1, 5 and 6 are used in conjunction with the following input parameter values: (i) the amplification λ of the outer mesh layer per normalized luminance unit. OPL The value is 150 Hz; (ii) Bipolar inert leakage (iii) Feedback amplification λ A The Hz frequency is 100 Hz; (iv) the spatial scale σA is 2.5°; and (v) the temporal scale τA is 0.01 ms. The neuron bundles (1602) are arranged in a circular pattern spanning a 15° × 15° field of view.

[0421] The sparse lateral connectivity pattern of the virtual retina was used with 10 presynaptic neurons with 10% positive weights and a weight variance of 0.01. Furthermore, the supplementary high-pass filter option for the outer retina, as described in Equations 2 and 3, was used with the following parameter values: a time scale of 0.2 ms and a spatial scale of 0.5°. The postsynaptic pooling option was also turned off. Postprocessing of the computed simulated retinal image of the control (C8) glasses design of Example 8 using the virtual retina platform as described herein generated a spike sequence as a function of time for cells with both light-giving and light-removing polarities. Figure 70 The histogram of surrounding stimuli, which is highlighted as a function of time, shows the average peak rate. Figure 71 ). Figure 70 and Figure 71 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0422] Post-processing of the computed simulated retinal image of the glasses design of Example 8 (D8) using the virtual retinal platform as described herein generated a sequence of spikes as a function of time for cells having both light-giving and light-removing polarities. Figure 72 The histogram of surrounding stimuli, which is highlighted as a function of time, shows the average peak rate. Figure 73 ). Figure 72 and Figure 73 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0423] The depiction obtained by comparing with the (C8) spectacle lens is as follows Figure 70 The neuronal activity of the spike sequence as a function of time is relatively constant over time, or exhibits minimal change, no change, or no fluctuation. This observation is similar for cells with two types of polarity—light-giving polarity and light-removing polarity. On the other hand, the depiction obtained through the spectacle lens of embodiment (D8) is... Figure 72 The neuronal activity in the spike sequence is relatively time-varying, exhibiting fluctuations over time. The observed time-dependent fluctuations are periodic, with the observed fluctuations having small amplitudes. The instability and nonlinearity in the spike response obtained by implementing the lens are attributed to artificial edges or luminous contrast contours in the retinal image, or the temporal variation of the artificial edges.

[0424] In Example 8, the depiction of the lens of the (C8) eyeglasses is shown as... Figure 71 The average peak rate of neuronal activity follows a relatively monotonous profile after the initial 100 milliseconds representing signal stabilization. This observed pattern is similar for cells with two types of polarity—light-giving polarity and light-removing polarity.

[0425] On the other hand, for both light-providing and light-removing cells, the description obtained by the spectacle lens in embodiment (D8) is as follows: Figure 73 The average peak rate of neuronal activity follows a pattern that varies over time. In this example 8, on-axis and off-axis evaluations of optical performance are modeled using a photometric function describing the average spectral sensitivity of human visual perception of brightness in a multicolor mode spanning wavelengths from 470 nm to 650 nm at a pupil analysis diameter of 6 mm under photopic conditions.

[0426] As in this article Figure 74 and Figure 75The wide-area optical performance, measured using a modulation transfer function as a function of spatial frequency at a pupil diameter of 6 mm, is virtually indistinguishable between the control (C8) spectacle lens (represented by a solid black line) and the exemplary embodiment (D8) spectacle lens (represented by a dashed black line). In Example 8, for off-axis performance, a field of view of 20° is considered for performance evaluation, i.e., ±10° from the center.

[0427] Example 9 – Comparison (C9) Design and Exemplary Implementation (D9) Design

[0428] In this Example 9, the following parameters of the illustrative model eye in Table 1 are changed to represent a 1D myopic eye in its 1D adaptation state (i.e., the basic prescription Rx is -3D): (i) the vitreous cavity depth of the eyepiece is 16.92 mm, (ii) the retinal curvature radius is 12 mm, and (iii) the parameters of anterior lens radius (R = 9.34 mm) and conic constant (Q = -3.2).

[0429] The model is configured to focus on a distant object 1 meter from the eye. A modified myopia schematic model eye is corrected one at a time using a control (C9) spectacle lens and an exemplary embodiment (D9) spectacle lens. The control (C9) spectacle lens represents a single-vision lens modeled using the following parameters: anterior surface (R = 2000 mm), center thickness (1.5 mm), posterior surface (R = 379.1 mm), and refractive index of 1.5, as well as a total blank diameter of 50 mm. The control spectacle lens C9 has none of the non-refractive features contemplated in this disclosure.

[0430] The second lens D9 represents the following exemplary embodiment: this exemplary embodiment is also a single-vision lens having the same parameters as the reference C9, and this exemplary embodiment is further configured with Figure 76 The non-refractive characteristics disclosed in the paper.

[0431] The non-refractive feature of Exemplary Implementation Example D9 includes a square grid pattern (7602) that also includes a plurality of square apertures positioned around the optical center of the spectacle lens (7601). The total number of apertures designed within the pattern (7602) is approximately 16. The total size of the square grid is approximately 3 mm × 3 mm. The width of the lines or boundaries forming the square apertures is approximately between 50 μm (7604). The remainder (7605) of Exemplary Implementation Example D9 is configured with single-vision parameters matching the basic prescription of the eye. The non-refractive feature of Exemplary Implementation Example D9 is configured such that it absorbs at least 85% of the light incident on the non-refractive feature.

[0432] Following the steps disclosed in paragraphs

[00385] to

[00387] , when the C9 glasses design and the D9 glasses design are fitted onto the illustrative model eye of Example 9, a simulated retinal image is calculated and analyzed by comparing it with the C9 glasses design and the D9 glasses design. In this Example 9, additional variables of the virtual retinal platform are conceived to have the following settings; the option of the contrast gain control mechanism described in Equations 1, 5, and 6 is [option missing]. The arrangement of the neuron bundles (1602) is a circular arrangement spanning a 20° × 20° field of view.

[0433] The sparse lateral connectivity pattern of the virtual retina was used with 10 presynaptic neurons with 10% positive weights and a weight variance of 0.01. The supplementary high-pass filter option for the outer reticular layer described in Equations 2 and 3 was turned off. The postsynaptic pooling option was also turned off.

[0434] Post-processing of the calculated simulated retinal image of the control (C9) glasses design of Example 9 was performed using the virtual retinal platform as described herein, generating a sequence of spikes as a function of time for cells having both light-giving and light-reducing polarities. Figure 77 The histogram of surrounding stimuli, which is highlighted as a function of time, shows the average peak rate. Figure 78 ). Figure 77 and Figure 78 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0435] Post-processing of the computed simulated retinal image of the glasses design of Example 9 (D9) using the virtual retinal platform as described herein generated a sequence of spikes as a function of time for cells having both light-giving and light-reducing polarities. Figure 79 The histogram of surrounding stimuli, which is highlighted as a function of time, shows the average peak rate. Figure 80 ). Figure 79 and Figure 80 The top and bottom subplots represent data for illuminated and deiled cells, respectively.

[0436] For cells exhibiting both light-giving and light-removing polarities, the depiction obtained using a control (C9) spectacle lens is as follows: Figure 77 The neuronal activity of the spike sequence as a function of time is relatively constant over time, or exhibits minimal change, no change, or no fluctuation. On the other hand, the description of the spectacle lens by embodiment (D9) is as follows: Figure 79 The neuronal activity of the spike sequence, as a function of time, is relatively time-varying and fluctuates with varying periodicity. In Example 9, the depiction obtained by means of the (C9) spectacle lens is as follows: Figure 78The average peak rate of neuronal activity follows a relatively monotonous profile after the initial 50 milliseconds representing signal stabilization. This observed pattern is similar for cells with both light-giving and light-removing polarities. The light-removing polarity cell response shows some variation in the average peak rate over time; however, the magnitude of this variation is small. On the other hand, for both light-giving and light-removing cells, the depiction obtained by the spectacle lens in embodiment (D9) is as follows: Figure 80 The average peak rate of neuronal activity, as a function of time, follows a pattern that varies over time. For both types of polarity, the depiction obtained through the contrast (C9) spectacle lens is as follows: Figure 77 The neuronal activity in the spike sequence is relatively constant over time. The instability and nonlinearity in the spike response obtained by implementing the lens are attributed to artificial edges or luminous contrast contours in the retinal image, or the temporal variation of the artificial edges.

[0437] As can be seen from the response of discrete neuronal bundles, the number of active discrete light-reducing neuronal bundles is 3 to 4 times lower than the corresponding number of active discrete light-giving neuronal bundles. On the other hand, the description obtained by the spectacle lens in embodiment (D9) is as follows: Figure 79 The neuronal activity of the spike sequence is relatively time-varying for both types of polarity. Furthermore, the total number of active, refractory discrete neuronal bundles can be comparable to the number of active, illuminated discrete neuronal bundles.

[0438] In Example 9, on-axis and off-axis evaluations of optical performance are modeled in monochromatic mode (589 nm) with a pupil analysis diameter of 5 mm. As described in this paper... Figure 81 and Figure 82 The wide-area optical performance measured using the modulation transfer function as a function of spatial frequency at a pupil diameter of 5 mm is virtually indistinguishable between the control (C9) contact lens and the exemplary embodiment (D9) spectacle lens. In Example 9, for off-axis performance, the field of view considered for performance evaluation is 20°, i.e., ±10° from the center.

[0439] Example 10 – Comparative (C10) Design and Exemplary Implementation (D10) Design

[0440] In this Example 10, the following parameters of the illustrative model eye in Table 1 are changed to represent a 4D myopic eye in its 2D adaptation state (i.e., the basic prescription Rx is -4D): (i) the vitreous cavity depth of the eyepiece is 18 mm, (ii) the retinal curvature radius is 12 mm, and (iii) the parameters of anterior lens radius (R = 7.934 mm) and conic constant (Q = -1.962).

[0441] The model is configured to focus on a distant object 50 cm from the eye. A modified myopia-illustrating model eye is corrected one at a time using a control (C10) spectacle lens and an exemplary embodiment (D10) spectacle lens. The control (C10) spectacle lens represents a single-vision lens modeled using the following parameters: anterior surface area (R = 2000 mm), center thickness (1.5 mm), posterior surface area (R = 102.26 mm), refractive index of 1.5, and a total blank diameter of 50 mm. The control spectacle lens C10 has none of the non-refractive features contemplated in this disclosure.

[0442] The second lens D10 represents the following exemplary embodiment: this exemplary embodiment is also a single-vision lens having the same parameters as the reference C10, and this exemplary embodiment is further configured with Figure 83 The non-refractive features disclosed herein. The non-refractive features of exemplary embodiment D10 include a non-refractive feature configured as a random pattern (8302), which further includes a series of lines or stripes positioned around the optical center of the spectacle lens (8301). The total number of lines or stripes designed within the pattern (8302) is approximately 16. The length (8306) of the lines or stripes is approximately between 0.75 mm and 1.25 mm.

[0443] The width of the line or stripe (8304) is approximately between 25 μm and 75 μm. The remainder (8305) of the exemplary embodiment D10 is configured with single-vision parameters matching the basic prescription of the eye. The non-refractive feature of the exemplary embodiment D10 is configured such that it absorbs at least 80% of the light incident on the non-refractive feature.

[0444] Following the steps disclosed in paragraphs

[00385] to

[00387] , simulated retinal images were calculated and analyzed using the C10 glasses design and the D10 glasses design as opposed to those of Example 10, when fitted onto the illustrative model eye of Example 10. In this Example 10, additional variables of the virtual retinal platform were conceived to have the following settings; the option for the contrast gain control mechanism described in Equations 1, 5, and 6 was: The arrangement of the neuronal bundles (1602) was a circular arrangement spanning a 20° × 20° field of view. The sparse lateral connectivity mode of the virtual retina was turned off. The supplementary high-pass filter option for the outer retina described in Equations 2 and 3 was turned off. The postsynaptic pooling option was also turned off. The calculated simulated retinal image of the control (C10) glasses design of Example 10 was post-processed using the virtual retinal platform as described herein, generating a spike sequence as a function of time for cells having both light-giving and light-reducing polarities. Figure 84The histogram of surrounding stimuli, which is highlighted as a function of time, shows the average peak rate. Figure 85 ). Figure 84 and Figure 85 The top and bottom subplots represent data for illuminated and deilluminated cells, respectively. Post-processing of the computed simulated retinal image of the glasses design of Example 10 (D10) using a virtual retina platform as described herein generated a sequence of spikes as a function of time for cells exhibiting both illuminated and deilluminated polarities. Figure 86 The histogram of surrounding stimuli, which is highlighted as a function of time, shows the average peak rate. Figure 87 ).

[0445] Figure 86 and Figure 87 The top and bottom subplots represent data for illuminated and deiled cells, respectively. The depiction obtained using a control (C10) spectacle lens is as follows: Figure 84 The spike sequence of neuronal activity corresponds to two types of polarity—namely, light-giving cells (…). Figure 84 (top sub-image) and faded type cells ( Figure 84 The bottom subgraph (which is relatively constant over time) represents the response of discrete neuron bundles.

[0446] As can be seen, the number of active discrete light-reducing neuronal bundles is 3 to 4 times lower than the corresponding number of active discrete light-giving neuronal bundles. On the other hand, the depiction obtained by the spectacle lens in embodiment (D10) is as follows... Figure 86 The spike sequence of neuronal activity—for two types of polarity, namely light-bearing cells ( Figure 86 (top sub-image) and faded cells ( Figure 86 (The bottom sub-figure) - is relatively time-varying. However, through the example of the spectacle lens in embodiment (D10), the total number of active light-reducing discrete neuron bundles can be comparable to the number of active light-giving discrete neuron bundles.

[0447] In Example 10, for light-bearing cells ( Figure 85 The top sub-figure), depicted by comparison with the (C10) spectacle lens, is Figure 85 The average peak rate of neuronal activity follows a relatively monotonous profile after the initial 50 milliseconds representing signal stabilization. On the other hand, bleached cells show some variation in the average peak rate over time; however, these variations are small in magnitude.

[0448] In contrast, the description obtained from the spectacle lens according to embodiment (D10) is as follows: Figure 87Discrete neuronal activity, with its average peak rate, varies over time. A time-varying pattern was observed in both illuminated and deiled cells; however, this pattern was more pronounced in deiled cells. In deiled cells (… Figure 87 The pattern observed in the bottom subplot (between time points 2000 ms and 3000 ms) shows that the average peak rate follows a quasi-sinusoidal pattern. At various other time points in the light-reduced cell response, the amplitude of the quasi-sinusoidal pattern decreases. The light-receiving cell response also shows a variation in the average peak rate over time; however, the magnitude of this variation is smaller.

[0449] The instability and nonlinearity in the peak response obtained by implementing the lens are attributed to artificial edges or luminous contrast profiles in the retinal image, or the temporal variation of artificial edges. In Example 10, on-axis and off-axis evaluations of optical performance were modeled using a photometric function describing the average spectral sensitivity of human visual perception of brightness in a multicolor mode spanning wavelengths from 470 nm to 650 nm under photopic vision conditions and with a pupil analysis diameter of 4 mm.

[0450] As in this article Figure 88 and Figure 89 The wide-area optical performance, measured using a modulation transfer function as a function of spatial frequency at a pupil diameter of 4 mm, is substantially similar between the control (C10) spectacle lens (represented by a solid black line) and the exemplary embodiment (D10) spectacle lens (represented by a dashed line). In Example 10, for off-axis performance, a field of view of 20° is considered for performance evaluation, i.e., ±10° from the center.

[0451] Example group A

[0452] A contact lens for an eye, the contact lens comprising: an anterior surface; a posterior surface; an optical region including a basic prescription for providing basic correction of distance refractive errors of the eye and a plurality of non-refractive features; and a peripheral region surrounding the optical region.

[0453] The contact lens according to the above example of Group A, wherein the basic prescription for the eye includes at least one of the following: spherical correction, astigmatism correction, or spherical and astigmatism correction.

[0454] The contact lens according to one or more of the above examples of Group A, wherein the plurality of non-refractive features includes at least one of the following: a plurality of generally opaque boundaries forming a plurality of apertures, wherein each aperture surrounds a generally transparent area, or the plurality of generally opaque features forming one or more patterns without generally distinct boundaries.

[0455] The contact lens according to one or more of the above examples of Group A, wherein each substantially transparent region includes the basic prescription for the eye.

[0456] The contact lens according to one or more of the above examples of Group A, wherein at least one of the plurality of apertures is circular, elliptical, oval, triangular, rectangular, square, pentagonal or hexagonal or octagonal, or any other regular or irregular polygon, or random shape.

[0457] The contact lens according to one or more of the above examples of Group A, wherein the plurality of apertures are configured in a circular, hexagonal, radial, spiral, regular, irregular or random arrangement.

[0458] The contact lens according to one or more of the above examples of Group A, wherein the surface area of ​​the transparent region surrounded by at least one of the plurality of apertures is between 0.25 square millimeters and 2.5 square millimeters, or between 0.5 square millimeters and 5 square millimeters, or between 0.75 square millimeters and 7.5 square millimeters, or between 0.25 square millimeters and 7.5 square millimeters.

[0459] According to one or more of the above examples of Group A, the contact lens wherein the width of the generally opaque boundary of any of the plurality of apertures is at least 3 times, at least 4 times, or at least 6 times, or at least 8 times, or at least 10 times the average wavelength of the visible spectrum (i.e., 555 nm), such that the generally opaque boundary remains substantially diffractive.

[0460] The contact lens according to one or more of the above examples of Group A, wherein the width of the generally opaque boundary of any of the plurality of apertures is between 5 μm and 75 μm, or between 25 μm and 150 μm, or between 50 μm and 250 μm.

[0461] The contact lens according to one or more of the above examples of Group A, wherein the total number of orifices in the plurality of orifices is at least 2, at least 3, at least 4, at least 5, at least 6, or at least 7 orifices.

[0462] According to one or more of the above examples of Group A, the contact lens, wherein the plurality of patterns without generally distinct boundaries includes at least: spoke wheel pattern, spiral pattern, vortex pattern, grid pattern, Memphis pattern, dot pattern, regular pattern, irregular pattern, moiré fringe pattern, interference pattern, random pattern with dots, random pattern with straight lines, random pattern with non-circular dots, random pattern with curves, random pattern with arcs, and random pattern with zigzag lines; wherein each of the plurality of patterns forms a generally opaque feature including dots, lines, or stripes.

[0463] A contact lens according to one or more of the above examples of Group A, wherein a plurality of patterns without generally distinct boundaries are centered or off-center within the optical area.

[0464] According to one or more of the above examples of Group A, the contact lens wherein the total surface area of ​​the plurality of non-refractive features occupies between 2.5% and 10%, or between 5% and 15%, or between 7.5% and 20% of the total surface area of ​​the optical zone.

[0465] The contact lens according to one or more of the above examples of Group A, wherein the plurality of non-refractive features are configured to be located within 3 mm, 4 mm, 5 mm or 6 mm of the center of the optical zone.

[0466] According to one or more of the above examples of Group A, the contact lens wherein the area located outside the center 6.5 mm, or outside the center 7 mm, or outside the center 7.5 mm of the optical zone is substantially free of the non-refractive features.

[0467] A contact lens according to one or more of the above examples of Group A, wherein the plurality of non-refractive features are applied to the front surface or the rear surface, or both the front surface and the rear surface.

[0468] A contact lens according to one or more of the above examples of Group A, wherein the plurality of non-refractive features are applied to the substrate of the contact lens.

[0469] The contact lens according to one or more of the above examples of Group A, wherein the total transmittance through the optical region is between 85% and 90%, or between 90% and 95%, or between 92.5% and 97.5%, or between 85% and 99%, of the total transmittance through the optical region of a similar single-view lens without the non-refractive feature.

[0470] A contact lens according to one or more of the above examples of Group A, wherein the plurality of non-refractive features are at least partially configured to be sensitive to the polarization of the incident light.

[0471] A contact lens according to one or more of the above examples of Group A, wherein the plurality of non-refractive features are activated and become opaque at least in part when the incident light is linearly, or circularly, or elliptically polarized.

[0472] A contact lens according to one or more of the above examples of Group A, wherein the plurality of non-refractive features are enabled and become opaque at least in part when the incident light comes from an LCD or LED or OLED monitor screen, TV screen, tablet screen or mobile phone screen or similar electronic device screen.

[0473] The contact lens according to one or more of the above examples of Group A, wherein the plurality of non-refractive features are at least partially configured to be electronically adjustable.

[0474] The contact lens according to one or more of the above examples of Group A, wherein the non-refractive feature is configured such that the material properties are spectrally sensitive to a specific visible wavelength between 420 nm and 760 nm, including the end values.

[0475] A contact lens according to one or more of the examples above in Group A, wherein the lens is capable of providing the wearer with visual performance that is substantially similar to that obtained using a single-vision lens without non-refractive features.

[0476] The contact lens according to one or more of the above examples of Group A, wherein the non-refractive feature is configured such that the material properties are spectrally sensitive to a specific visible wavelength between 420 nm and 760 nm.

[0477] According to one or more of the examples above in Group A, when tested on a model eye with a distance refractive error configured to substantially match the basic prescription, the contact lens provides an on-axis modulation transfer function for at least one pupil between 3 mm and 6 mm and including an end value, and at least one wavelength between 420 nm and 760 nm and including an end value, the on-axis modulation transfer function being substantially equal to the on-axis modulation transfer function obtained by a single-vision contact lens without the non-refractive feature.

[0478] According to one or more of the examples above in Group A, when tested on a model eye with a distance refractive error configured to substantially match the basic prescription, the contact lens provides an off-axis wide-area modulation transfer function for at least one pupil between 3 mm and 6 mm and including an end value, and at least one wavelength between 420 nm and 760 nm and including an end value, the off-axis wide-area modulation transfer function being substantially equal to the off-axis wide-area modulation transfer function obtained by a single-vision contact lens without the non-refractive features.

[0479] The contact lens according to one or more of the above examples of Group A, wherein the wide-field retina includes a field of view of at least 5°, or 10°, or 15°, or 20°, or 25°, or 30°.

[0480] According to one or more of the examples above in Group A, when tested on a model eye configured with a distance refractive error substantially matching the basic prescription, the contact lens provides basic correction of the distance refractive error of the eye and produces an artificial rim or spatial luminous contrast profile distributed over a wide area of ​​the retina of the model eye.

[0481] According to one or more of the examples above in Group A, when the contact lens is tested at various off-center positions on a model eye configured with a distance refractive error substantially matching the basic prescription, the contact lens provides a time-varying pattern of the artificial rim or spatial luminous contrast profile distributed over a wide area of ​​the retina of the model eye, the various off-center positions being used to simulate one of: supra-ocular movements of the contact lens; eye movements of the wearer; or a combination of supra-ocular movements of the contact lens and eye movements of the wearer.

[0482] The contact lens according to one or more of the above examples of Group A, wherein the model eye is schematic, physical, or benchtop model eye.

[0483] According to one or more of the examples above in Group A, the contact lens produces a basic correction of the distance refractive error of the model eye when tested on a desktop or physical model eye configured to substantially match the basic prescription for the distance refractive error.

[0484] According to one or more of the above examples of Group A, the contact lens, wherein the retina of the model eye, including a tabletop or physical one with a camera, is configured to capture an image of a visual scene projected through the model eye corrected by the contact lens, the camera having a charge-coupled device or a complementary metal oxide sensor.

[0485] According to one or more of the above examples of Group A, the contact lens wherein the image captured by the retina of the model eye is used as an input stream for a virtual retinal simulator, the virtual retinal simulator comprising at least one of the following three image processing steps disclosed herein: (a) spatiotemporally filtering the input stream of the image to generate a bandpass current, (b) performing instantaneous nonlinear contrast gain control using a variable feedback gate parallel conductance, and (c) noise integration and generating a discrete set of excited cell models to produce a spike sequence depicting ganglion cell activity.

[0486] A contact lens according to one or more of the examples above in Group A, wherein the plurality of non-refractive regions are configured to provide increased retinal ganglion cell activity compared to retinal ganglion cell activity obtained by a single-view contact lens without the non-refractive features.

[0487] The contact lens according to one or more of the examples above in Group A, wherein the retinal ganglion cell activity is at least 1.25 times, 1.5 times, 1.75 times, 2 times, 2.25 times, 2.5 times, 2.75 times, or 3 times the retinal ganglion cell activity of a single-vision contact lens without the non-refractive features, and the retinal ganglion cell activity is measured as the average retinal peak rate integrated over a specific time range.

[0488] The contact lens according to one or more of the above examples of Group A, wherein the specific time range can be at least 1 second, or at least 3 seconds, or at least 10 seconds, or at least 30 seconds, or at least 60 seconds, or at least 120 seconds, or at least 180 seconds, and the average retinal peak rate is integrated over the specific time range.

[0489] According to one or more of the above examples of Group A, the instability in the retinal ganglion cell activity or neuronal response, measured as the average retinal peak rate, is observed in the retinal field of the illuminated center / removed periphery, or in the retinal field of the illuminated periphery / removed center, or in both the retinal field of the illuminated center / removed periphery and the retinal field of the illuminated periphery / removed center.

[0490] According to one or more of the above examples of Group A, the contact lens wherein the instability in the neuronal response, as a function describing the overall retinal ganglion cell activity at the retina of the model eye or as measured by the average retinal peak rate as a function of time, follows a nonlinear or periodic, sinusoidal or quasi-sinusoidal, rectangular, quasi-rectangular, square, quasi-square, or non-monotonic pattern depicting the time-varying activity of the overall retinal ganglion cell activity.

[0491] The contact lens according to one or more of the above examples of Group A, wherein the plurality of non-refractive features provide at least one of slowing myopia progression, delaying myopia progression, or preventing myopia progression, the myopia progression being measured by a change in the axial length of the eye or a change in distance refractive error.

[0492] A contact lens according to one or more of the examples above in Group A, wherein the contact lens provides at least partially adequate foveal correction for the refractive error of the eye, and the non-refractive feature provides at least partially a stop signal that varies over time and / or spatially to reduce the rate of myopia progression.

[0493] The contact lens according to one or more of the above examples of Group A, wherein the effectiveness of at least one of slowing myopia progression, delaying myopia progression, or preventing myopia progression is maintained for at least 12 months, 24 months, 36 months, 48 ​​months, or 60 months of lens wear.

[0494] A contact lens according to one or more of the above examples of Group A, wherein the peripheral region does not have the plurality of generally opaque features.

[0495] The contact lens according to one or more of the above examples of Group A, wherein the non-refractive feature is applied using pad printing, laser etching, photolithography or laser printing.

[0496] A contact lens described in one or more of the above examples of Group A, in combination with one or more of the eyeglass lens examples according to Example Group B, constitutes an additional embodiment.

[0497] Example group B

[0498] An eyeglass lens for an eye includes: a convex surface; a concave surface; an optical center, around which a basic prescription is arranged to provide basic correction for distance refractive errors of the eye, and the eyeglass lens also includes a plurality of non-refractive features.

[0499] According to the above examples of group B, the spectacle lens, wherein the basic prescription for the eye includes at least one of the following: spherical correction, astigmatism correction, or spherical and astigmatism correction.

[0500] The spectacle lens according to one or more of the above examples of Group B, wherein the plurality of non-refractive features includes at least one of the following: a plurality of generally opaque boundaries forming a plurality of apertures, wherein each aperture surrounds a generally transparent area; or, a plurality of generally opaque features forming one or more patterns without generally distinct boundaries.

[0501] The eyeglass lens according to one or more of the above examples of Group B, wherein each substantially transparent area includes the basic prescription for the eye.

[0502] According to one or more of the above examples of Group B, the eyeglass lens is wherein at least one of the plurality of apertures is circular, elliptical, oval, triangular, rectangular, square, pentagonal, hexagonal, or octagonal, or any other regular or irregular polygon, or random shape.

[0503] According to one or more of the above examples of Group B, the surface area of ​​the transparent region surrounded by at least one of the plurality of apertures is between 0.25 square millimeters and 2.5 square millimeters, or between 0.5 square millimeters and 5 square millimeters, or between 0.75 square millimeters and 7.5 square millimeters, or between 0.25 square millimeters and 7.5 square millimeters.

[0504] According to one or more of the above examples of Group B, the eyeglass lens wherein the width of the generally opaque boundary of any of the plurality of apertures is at least 3 times, at least 4 times, or at least 6 times, or at least 8 times, or at least 10 times the average wavelength of the visible spectrum (i.e., 555 nm), such that the generally opaque boundary remains substantially diffractive.

[0505] According to one or more of the above examples of Group B, the eyeglass lens wherein the width of the generally opaque boundary of any of the plurality of apertures is between 5 μm and 75 μm, or between 25 μm and 150 μm, or between 50 μm and 250 μm.

[0506] The eyeglass lens according to one or more of the above examples of Group B, wherein the total number of the plurality of apertures is at least 6, at least 9, at least 12, at least 18, at least 24, or at least 30 apertures.

[0507] The eyeglass lens according to one or more of the above examples of Group B, wherein the plurality of apertures are configured in a circular, hexagonal, radial, spiral, regular, irregular or random arrangement.

[0508] According to one or more of the above examples of Group B, the eyeglass lens, wherein the plurality of patterns without generally distinct boundaries includes at least: spoke wheel pattern, spiral pattern, vortex pattern, grid pattern, Memphis pattern, dot pattern, regular pattern, irregular pattern, moiré fringe pattern, interference pattern, random pattern with dots, random pattern with straight lines, random pattern with non-circular dots, random pattern with curves, random pattern with arcs, and random pattern with zigzag lines; wherein each of the plurality of patterns forms a generally opaque feature including dots, lines, or stripes.

[0509] According to one or more of the above examples of Group B, the spectacle lens wherein multiple patterns without generally distinct boundaries are centered or off-center within the spectacle lens.

[0510] According to one or more of the above examples of Group B, the total surface area of ​​the plurality of non-refractive features occupies between 5% and 15%, or between 7.5% and 20%, or between 12.5% ​​and 25% of the total surface area of ​​the eyeglass lens.

[0511] According to one or more of the above examples of Group B, the spectacle lens wherein the plurality of non-refractive features are configured to be located within 10 mm, 15 mm, 20 mm or 30 mm of the center of the spectacle lens.

[0512] According to one or more of the above examples of Group B, the spectacle lens, wherein the area located outside the center 30 mm, or outside the center 35 mm, or outside the center 40 mm of the spectacle lens is substantially devoid of the non-refractive features.

[0513] The spectacle lens according to one or more of the above examples of Group B, wherein the plurality of non-refractive features are applied to the front surface, or the rear surface, or both the front surface and the rear surface.

[0514] The spectacle lens according to one or more of the above examples of Group B, wherein the plurality of non-refractive features are applied to the matrix of the spectacle lens.

[0515] According to one or more of the above examples of Group B, the spectacle lens wherein the substantially opaque boundary or feature is configured such that the substantially opaque boundary or feature absorbs at least 80%, at least 90%, or at least 99% of the light incident on the substantially opaque boundary or feature.

[0516] According to one or more of the above examples of Group B, the total light transmittance through the optical zone is between 85% and 90%, or between 90% and 95%, or between 92.5% and 97.5%, or between 85% and 99% of the total light transmittance through the optical zone of a similar single-vision lens without the said non-refractive feature.

[0517] The spectacle lens according to one or more of the above examples of Group B, wherein the plurality of non-refractive features are at least partially configured to be sensitive to the polarization of incident light.

[0518] According to one or more of the above examples of Group B, the spectacle lens wherein the plurality of non-refractive features are activated and become opaque at least in part when the incident light is linearly, or circularly, or elliptically polarized.

[0519] The eyeglass lens according to one or more of the above examples of Group B, wherein the plurality of non-refractive features are enabled and become opaque at least in part when the incident light comes from an LCD or LED or OLED monitor screen, TV screen, tablet screen or mobile phone screen or similar electronic device screen.

[0520] The spectacle lens according to one or more of the above examples of Group B, wherein the plurality of non-refractive features are at least partially configured to be electronically adjustable.

[0521] According to one or more of the above examples of Group B, the spectacle lens wherein the non-refractive feature is configured such that the material properties are spectrally sensitive to a specific visible wavelength between 420 nm and 760 nm, including the end values.

[0522] The eyeglass lens according to one or more of the examples above in Group B, wherein the lens is capable of providing the wearer with visual performance that is substantially similar to that obtained using a single-vision lens without non-refractive features.

[0523] According to one or more of the examples in Group B above, when tested on a model eye configured with a distance refractive error substantially matching the basic prescription, the spectacle lens provides an on-axis modulation transfer function for at least one pupil between 3 mm and 6 mm and including an end value, and at least one wavelength between 420 nm and 760 nm and including an end value, the on-axis modulation transfer function being substantially equal to the on-axis modulation transfer function obtained by a single-vision spectacle lens without the non-refractive feature.

[0524] According to one or more of the examples in Group B above, when tested on a model eye configured with a distance refractive error substantially matching the basic prescription, the spectacle lens provides an off-axis wide-area modulation transfer function for at least one pupil between 3 mm and 6 mm and including an end value, and at least one wavelength between 420 nm and 760 nm and including an end value, the off-axis wide-area modulation transfer function being substantially equal to the off-axis wide-area modulation transfer function obtained by a single-vision spectacle lens without the non-refractive feature.

[0525] The spectacle lens according to one or more of the above examples of Group B, wherein the wide-field retina includes a field of view of at least 5°, or 10°, or 15°, or 20°, or 25°, or 30°.

[0526] According to one or more of the examples above in Group B, when tested on a model eye configured with a distance refractive error substantially matching the basic prescription, the spectacle lens provides basic correction to the distance refractive error of the eye and produces an artificial marginal or spatial luminous contrast profile distributed over a wide area of ​​the retina of the model eye.

[0527] According to one or more of the examples in Group B above, when various off-center positions used to simulate the wearer's eye movements are tested on a model eye configured with a distance refractive error that substantially matches the basic prescription, the spectacle lens provides a change over time in the artificial rim or spatial luminous contrast profile distributed over a wide area of ​​the retina of the model eye.

[0528] The eyeglass lens according to one or more of the above examples of Group B, wherein the model eye is schematic, physical, or benchtop model eye.

[0529] According to one or more of the examples in Group B above, when tested on a desktop or physical model eye configured to substantially match the distance refractive error of the model eye, the spectacle lens produces a basic correction of the distance refractive error of the model eye.

[0530] According to one or more of the above examples of Group B, the spectacle lens, wherein the retina of the model eye, including a tabletop or physical one with a camera, is configured to capture an image of a visual scene projected by the model eye corrected by the spectacle lens, the camera having a charge-coupled device or a complementary metal oxide sensor.

[0531] According to one or more of the above examples of Group B, the eyeglass lens, wherein the image captured by the retina of the model eye is used as an input stream for a virtual retinal simulator, the virtual retinal simulator comprising at least one of the following three image processing steps disclosed herein: (a) spatiotemporally filtering the input stream of the image to generate a bandpass current, (b) performing instantaneous nonlinear contrast gain control using a variable feedback gate parallel conductance, and (c) noise integration and generating a discrete set of excited cell models to produce a spike sequence depicting ganglion cell activity.

[0532] According to one or more of the above examples of Group B, the spectacle lens wherein the plurality of non-refractive regions are configured to provide increased retinal ganglion cell activity compared to that obtained by a single-vision spectacle lens without the non-refractive features.

[0533] According to one or more of the above examples of Group B, the spectacle lens, wherein the retinal ganglion cell activity is at least 1.25 times, 1.5 times, 1.75 times, 2 times, 2.25 times, 2.5 times, 2.75 times, or 3 times the retinal ganglion cell activity of a single spectacle lens without the non-refractive feature, and the retinal ganglion cell activity is measured as the average retinal peak rate integrated over a specific time range.

[0534] According to one or more of the above examples of Group B, the eyeglass lens wherein the specific time range can be at least 1 second, or at least 3 seconds, or at least 10 seconds, or at least 30 seconds, or at least 60 seconds, or at least 120 seconds, or at least 180 seconds, and the average retinal peak rate is integrated over the specific time range.

[0535] According to one or more of the above examples of Group B, the spectacle lens wherein the instability in the retinal ganglion cell activity or neuronal response, measured as the average retinal peak rate, is observed in the retinal field of the illuminated center / removed periphery, or in the retinal field of the illuminated periphery / removed center, or in both the retinal field of the illuminated center / removed periphery and the retinal field of the illuminated periphery / removed center.

[0536] According to one or more of the above examples of Group B, the spectacle lens wherein the instability in the neuronal response, as a function describing the overall retinal ganglion cell activity at the retina of the model eye or as measured by the average retinal peak rate as a function of time, follows a nonlinear or periodic, sinusoidal or quasi-sinusoidal, rectangular wave, quasi-rectangular wave, square wave, quasi-square wave, or non-monotonic pattern depicting the time-varying activity of the overall retinal ganglion cell activity.

[0537] According to one or more of the above examples of Group B, the spectacle lens, wherein the plurality of non-refractive features provides at least one of slowing myopia progression, delaying myopia progression, or preventing myopia progression, the myopia progression being measured by a change in the axial length of the eye or a change in distance refractive error.

[0538] According to one or more of the above examples of Group B, the spectacle lens provides at least partially sufficient foveal correction for the refractive error of the eye, and the non-refractive feature provides at least partially a stop signal that varies over time and / or spatially to reduce the rate of myopia progression.

[0539] According to one or more of the above examples of Group B, the spectacle lens, wherein the effectiveness of at least one of slowing myopia progression, delaying myopia progression, or preventing myopia progression is maintained for at least 12 months, 24 months, 36 months, 48 ​​months, or 60 months of lens wear.

[0540] The eyeglass lens according to one or more of the above examples of Group B, wherein the peripheral region does not have the plurality of generally opaque features.

[0541] The spectacle lens according to one or more of the above examples of Group B, wherein the non-refractive feature is applied using pad printing, laser etching, photolithography or laser printing.

[0542] An eyeglass lens according to one or more of the above examples of Group B, combined with one or more of the contact lens examples according to Example Group A, constitutes another embodiment.

Claims

1. An ophthalmic lens for an eye, the ophthalmic lens comprising an anterior surface, a posterior surface, an optical center, and an optical region surrounding the optical center, the optical region comprising a basic prescription for the eye and a plurality of non-refractive features; wherein, The basic prescription includes spherical correction, astigmatism correction, or spherical and astigmatism correction.

2. The lens according to claim 1, wherein, The plurality of non-refractive features include a plurality of generally opaque boundaries forming a plurality of apertures, wherein each aperture surrounds a generally transparent region; wherein each generally transparent region includes the basic prescription for the eye.

3. The lens according to claim 2, wherein, The shape of at least one of the plurality of generally opaque boundaries forming the plurality of apertures is circular, elliptical, oval, triangular, rectangular, square, pentagonal, hexagonal, octagonal, or any other regular polygon, irregular polygon, or random shape; and wherein the surface area of ​​the transparent region surrounded by at least one of the plurality of apertures is between 0.25 square millimeters and 7.5 square millimeters.

4. The lens according to claim 3, wherein, The plurality of orifices are configured in a circular, hexagonal, radial, spiral, regular, irregular, or random arrangement.

5. The lens according to any one of claims 1 to 4, wherein, The width of the substantially opaque boundary is at least three times the average wavelength of the visible spectrum (i.e., 555 nm), such that the substantially opaque boundary remains substantially diffractive.

6. The lens according to claim 5, wherein, The width of the generally opaque boundary of any of the plurality of orifices is between 5 μm and 250 μm.

7. The lens according to claim 1, wherein, The plurality of non-refractive features form at least one pattern without generally distinct boundaries, wherein the pattern includes: spoke wheel pattern, spiral pattern, vortex pattern, grid pattern, Memphis pattern, dot pattern, regular pattern, irregular pattern, moiré fringe pattern, interference pattern, random pattern with dots, random pattern with straight lines, random pattern with non-circular dots, random pattern with curves, random pattern with arcs, and random pattern with zigzag lines; wherein each of the plurality of patterns forms a generally opaque feature including dots, lines, or stripes.

8. The lens according to claim 7, wherein, The width of the substantially opaque feature is at least 5 μm and no more than 250 μm.

9. The lens according to any one of the preceding claims, wherein, The plurality of non-refractive features are centered or off-center within the optical region.

10. The lens according to any one of the preceding claims, wherein, The total surface area of ​​the plurality of non-refractive features occupies between 2.5% and 15% of the total surface area of ​​the optical region.

Images