Ophthalmic lenses for the treatment of myopia

Abstract

Ophthalmic lenses for the treatment of myopia, methods for forming such lenses, methods for using such lenses, and methods for monitoring the effectiveness of such lenses are provided. [Solution] The lenses include a dot pattern distributed across each lens, the dot pattern including an array of dots spaced at a distance of 1 mm or less, each dot having a maximum dimension of 0.3 mm or less, the dot pattern including dot-free transparent gaps having a maximum dimension greater than 1 mm, the transparent gaps being aligned with the visual axis of the wearer of the glasses.

Description

[Technical field]

[0001] The present invention features ophthalmic lenses for the treatment of myopia, methods of making such lenses, methods of using such lenses, and methods for monitoring the effectiveness of such lenses. [Background technology]

[0002] The eye is an optical sensor in which light from an external source is focused by a lens onto the surface of the retina, which is an array of wavelength-dependent photosensors. Each of the various configurations in which the eye's lens is received is associated with a focal length at which external light rays are optimally or nearly optimally focused to produce an inverted image on the surface of the retina that corresponds to the external image observed by the eye. In each of the various configurations in which the eye's lens is received, the eye's lens optimally or nearly optimally focuses light emitted or reflected from external objects within a certain distance range from the eye, and less optimally or not able to focus on objects outside that distance range.

[0003] In individuals with normal vision, the axial length of the eye, or the distance from the lens to the retinal surface, corresponds to the focal length for approximately optimal focusing on distant objects. The eye of an individual with normal vision focuses on distant objects without neural input to the muscles that exert a force to change the shape of the eye's lens, called "accommodation." Nearer, near objects are focused on by the average individual as a result of accommodation.

[0004] However, many people suffer from disorders related to the axial length of the eye, such as myopia ("nearsightedness"). A myopic person has an eye with an axial length that is longer than the axial length required to focus on distant objects without accommodation. As a result, myopic people see close objects clearly, but more distant objects appear blurry. Myopic people are generally able to accommodate, but can focus on objects at a shorter average distance than people with normal vision.

[0005] Typically, infants are born hyperopic, with an axial length shorter than that required for optimal or near-optimal focusing on distant objects without accommodation. During normal development of the eye, called "emmetropization," the axial length increases relative to the other dimensions of the eye to a length that will nearly optimally focus on distant objects without accommodation. Ideally, as the eye grows to its final adult size, biological processes will maintain the axial length relative to the eye size at a near-optimal level. However, in myopic individuals, the axial length relative to the overall eye size continues to increase during development, exceeding the length that will nearly optimally focus on distant objects, leading to increasingly significant myopia.

[0006] Myopia is believed to be influenced by behavioral factors as well as genetic factors. Thus, myopia can be alleviated by a treatment device that addresses behavioral factors. For example, a treatment device for treating axial length-related disorders, including myopia, is described in U.S. Patent Application Publication No. 2011 / 0313058 A1. Summary of the Invention

[0007] Spectacles and contact lenses are disclosed that reduce retinal signals that cause axial length to increase. Exemplary embodiments are fabricated using polycarbonate or Tribex lens blanks that have been treated by applying a pattern of clear liquid plastic ridges that are cured and bonded to the lens by ultraviolet light. Each clear plastic ridge has a similar index of refraction to the underlying polycarbonate to which it is bonded, so that at the location of the ridges, the ridges and the underlying lens act as a single optical component. Such an array of optical components acts as a highly aberrated lens array that disperses light transmitted by the array fairly uniformly in all directions. The result is reduced contrast in the retinal image. The spectacle lenses have ridge-free gaps located at the lens axis that allow the user to experience maximum visual acuity when viewing on-axis objects, while objects at the periphery of the user's field of vision appear with reduced contrast and clarity.

[0008] In one example, the image on the retina consists of a normally focused image with an average luminosity of 74% of that which could be produced by the lens without the ridge array. Superimposed on the focused image is a background of uniform retinal illuminance equal to 25% of the average luminance of the normally focused image.

[0009] For these glasses, the contrast of the focused image is reduced compared to those normally used to correct (but not treat) refractive errors. The exact amount of contrast reduction depends on the relative amount of dark and light areas in the image transmitted. For the above example, when 24% of the light is uniformly distributed, the maximum contrast reduction can be 48%, where contrast is defined as luminance difference / average luminance. Experiments have demonstrated that this amount of contrast reduction has a significant effect on the physiology of the eye related to the mechanisms responsible for controlling the elongation of the axial length.

[0010] Various aspects of the invention are summarized below.

[0011] In general, in a first aspect, the invention features a pair of eyeglasses including an eyeglass frame and a pair of ophthalmic lenses mounted in the frame, the lenses including a pattern of dots distributed across each lens, the dot pattern including an array of dots spaced apart by a distance of 1 mm or less, each dot having a maximum dimension of 0.3 mm or less.

[0012] The implementation of the glasses may include one or more of the following features and / or features of other aspects. For example, each dot may have a maximum dimension of 0.2 mm or less (e.g., 0.1 mm or less, 0.05 mm or less, 0.02 mm or less, 0.01 mm or less). In some embodiments, each dot is approximately the same size. The dots may be spaced 0.8 mm or less (e.g., 0.6 mm or less, 0.5 mm or less, 0.4 mm or less, 0.35 mm or less). The dots may be arranged on a square grid, a hexagonal grid, other grid, or in a semi-random or random pattern. The dots may be spaced at regular intervals, such as 0.55 mm, 0.365 mm, or 0.24 mm. Alternatively, the dot spacing may vary with the distance of the dots from the center of the lens. For example, the dot spacing may monotonically increase or decrease as the distance from the center of the lens increases.

[0013] The dot pattern includes dot-free transparent gaps having a maximum dimension greater than 1 mm, the transparent gaps being aligned with the visual axis of the wearer of the eyeglasses. The transparent gaps can have a maximum dimension (e.g., diameter) of 2 mm or more (e.g., 3 mm or more, 4 mm or more, 5 mm or more, 6 mm or more, 7 mm or more, 8 mm or more) and up to 1.5 cm (e.g., 1.5 cm or less, 1.4 cm or less, 1.3 cm or less, 1.2 cm or less, 1.1 cm or less, 1.0 cm or less). The transparent gaps may be approximately circular or similar shapes, such as octagonal, square, or other polygonal shapes.

[0014] In some embodiments, the dots are bumps on the surface of the corresponding lens. The bumps may be formed of a transparent material. In some cases, the transparent material is clear and / or colorless. Alternatively or additionally, at least some of the transparent material may be colored (e.g., with a dye that absorbs red wavelengths). The transparent material may have substantially the same refractive index as the lens material. The bumps may be substantially spherical or hemispherical.

[0015] In some embodiments, the dots are depressions in the surface of the corresponding lens.

[0016] The dots may be inclusions between the facing surfaces of each lens.

[0017] The lenses may be clear lenses. In some embodiments, the lenses are tinted lenses.

[0018] The dot pattern reduces the image contrast of objects viewed through the dot pattern by at least 30% (e.g., at least 35%, at least 40%, at least 45%, at least 50%, at least 55%, at least 60%) compared to the image contrast of objects viewed through the transparent gap. In some embodiments, the lens has a refractive power that corrects the wearer's on-axis visual acuity through the transparent gap to 20 / 20 or better (e.g., 20 / 15), and for at least a portion of the wearer's peripheral vision through the dot pattern, the lens corrects the wearer's visual acuity to 20 / 25 or better, 20 / 30 or better, 20 / 40 or better, or the like.

[0019] In another aspect, the invention features a method of making eyeglasses that includes depositing individual quantities of material on a surface of a lens that correspond to a dot pattern and curing the deposited material to result in ridges on the lens surface that form the dot pattern. The material can be deposited using an inkjet printer. The deposited material can be cured using radiation (e.g., ultraviolet radiation).

[0020] In general, in another aspect, the invention features eyeglasses customized for a wearer, including an eyeglass frame and a set of ophthalmic lenses mounted in the frame, the lenses having a refractive power that corrects the wearer's on-axis visual acuity to 20 / 20 or better, the lenses including a dot pattern distributed across each lens, the dot pattern including an array of dots, the array of dots arranged such that for at least a portion of the wearer's peripheral vision, the lenses correct the wearer's visual acuity to 20 / 25 or better and reduce image contrast by at least 30% as compared to on-axis image contrast. Embodiments of the ophthalmic lenses can include one or more of the features of the other aspects.

[0021] In general, in a further aspect, the invention features eyeglasses customized for a wearer including an eyeglass frame and a set of ophthalmic lenses mounted in the frame, the lenses having a refractive power that corrects the wearer's on-axis visual acuity to 20 / 20 or better. The eyeglasses include an optical diffuser distributed across each lens, the optical diffuser configured such that, for at least a portion of the wearer's peripheral vision, the lenses correct the wearer's visual acuity to 20 / 40 or better, 20 / 30 or better, or 20 / 25 or better, and reduce image contrast by at least 30% as compared to on-axis image contrast.

[0022] The embodiment of the ophthalmic lens may include one or more of the following features and / or features of other aspects. For example, the optical diffuser may include a film laminated to a surface of each lens. The lenses may each include a transparent gap without an optical diffuser having a maximum dimension greater than 1 mm, the transparent gap being aligned with the visual axis of the wearer of the eyeglasses.

[0023] In general, in a further aspect, the invention features an ophthalmic lens including two opposing curved surfaces and a dot pattern distributed across each lens, the two opposing curved surfaces collectively having a refractive power that corrects a wearer's on-axis visual acuity to 20 / 20 or better, the dot pattern including an array of spaced dots, the dots arranged such that for at least a portion of the wearer's peripheral vision, the lens corrects the wearer's visual acuity to 20 / 25 or better and reduces image contrast by at least 30% compared to on-axis image contrast, and the dot pattern including clear gaps devoid of dots that are aligned with the wearer's visual axis.

[0024] Embodiments of the ophthalmic lens may include one or more of the following features and / or features of other aspects. For example, the ophthalmic lens may be a spectacle lens. Alternatively, in some embodiments, the ophthalmic lens is a contact lens.

[0025] In general, in another aspect, the invention features a method of monitoring and preventing the progression of myopia in a person that includes measuring a change in the person's choroidal thickness over a period of time and providing the person with an ophthalmic lens that reduces image contrast in the person's peripheral vision compared to on-axis image contrast.

[0026] Implementations of the method may include one or more of the following features and / or features of other aspects. For example, the ophthalmic lens may be provided in a pair of glasses of the aforementioned aspects. Alternatively, the ophthalmic lens may be provided as a contact lens. In some implementations, measuring the change includes measuring the thickness of the person's choroid using optical coherence tomography (OCT).

[0027] Among other advantages, the disclosed embodiments feature eyeglasses with features that reduce retinal signals that cause axial lengthening in the lenses of both eyes without reducing the user's on-axis visual acuity to an extent that causes confusion for the user. For example, a dot pattern that moderately blurs the wearer's peripheral vision while still allowing normal on-axis vision through a clear gap allows the wearer to use the eyeglasses all day, every day. The disclosed embodiments also allow the user to achieve therapeutic benefits in both eyes using only one pair of eyeglasses, as opposed to approaches that involve alternating between the use of different pairs of eyeglasses.

[0028] Additionally, the dot pattern can be largely unnoticeable to others, especially when the dot pattern is clear and colorless and / or when contact lenses are used. The subtlety of the dot pattern can result in more consistent use by some wearers, especially children who may be self-conscious about using a more noticeable device every day (e.g., at school or among peers). [Brief description of the drawings]

[0029] [Figure 1A] FIG. 1 shows a pair of glasses having ophthalmic lenses for treating myopia. [Figure 1B]FIG. 1B is a diagram showing a dot pattern on the ophthalmic lens shown in FIG. 1A. [Diagram 2] FIG. 2 illustrates the contrast reduction experienced using an exemplary ophthalmic lens for treating myopia. [Figure 3A] FIG. 1 illustrates an inkjet printing system for forming a dot pattern on an ophthalmic lens. [Figure 3B] FIG. 3B is a flow diagram showing steps in a method for creating a dot pattern using the system shown in FIG. 3A. [Figure 3C] FIG. 3C illustrates a print template for forming a dot pattern using the inkjet printing method of FIG. 3B. [Figure 3D] FIG. 2 is a top view of a fixture used to position multiple lenses in an inkjet printing system. [Figure 4] 1 is a photograph showing a dot pattern on an exemplary ophthalmic lens. [Diagram 5] Optical coherence tomography (OCT) image of the eye showing choroidal thickness. [Figure 6] 1 is an OCT image showing choroidal thickness. [Figure 7] FIG. 1 shows relative choroidal thickness as a function of retinal location before and after treatment in subjects. [Figure 8] Photograph showing the dot pattern used on the prototype I lens. [Figure 9] 1 compares the results of studies performed using the Prototype I lens and an earlier study. 2 shows the time course of axial length difference measurements. [Figure 10] Photograph showing the dot pattern used in the Prototype II lens. [Figure 11] Photograph showing the dot pattern used in the prototype III lens. [Figure 12] 1 is a bar graph comparing the change in diopters after 180 days for subjects from the initial study ("First Diffuser"), the Prototype III lens ("New Diffuser"), and the control group ("No Diffuser"). [Figure 13] FIG. 1 is a schematic diagram of a laser system for forming a dot pattern on a contact lens. [Figure 14A] FIG. 1 shows examples of dot patterns for contact lenses. [Figure 14B] FIG. 1 shows examples of dot patterns for contact lenses. [Figure 15A] 1 is a photograph of a contact lens having a dot pattern. [Figure 15B] 1 is a photograph of a spectacle lens having a dot pattern. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0030] 1A, myopia-reducing glasses are disclosed that can treat both eyes simultaneously without substantially compromising clear vision. Moreover, the glasses are sufficiently robust and unobtrusive that they do not break down and allow the wearer to engage in similar daily activities without being self-conscious about their appearance, which is particularly desirable since glasses are commonly used to halt the elongation of the axial length of children's eyes.

[0031] The myopia reduction glasses 100 are composed of a pair of frames 101 and ophthalmic lenses 110a and 110b attached to the frames. The ophthalmic lenses 110a and 110b have transparent gaps 120a and 120b, respectively, surrounded by contrast reduction areas 130a and 130b, respectively. The transparent gaps 120a and 120b are positioned to coincide with the wearer's on-axis viewing position, while the contrast reduction areas 130a and 130b correspond to the wearer's peripheral vision. Referring to FIG. 1B, the contrast reduction areas 130a and 130b are composed of an array of dots 140, which scatter light through these areas to the wearer's eye, thereby reducing the contrast of objects in the wearer's peripheral vision.

[0032] The size and shape of the transparent gap may vary. In general, the transparent gap provides the wearer with a visual cone such that the wearer's vision may be optimally corrected (e.g., 20 / 15 or 20 / 20). In some embodiments, the gap has a maximum dimension (in the xy plane) ranging from about 0.2 mm (e.g., about 0.3 mm or more, about 0.4 mm or more, about 0.5 mm or more, about 0.6 mm or more, about 0.7 mm or more, about 0.8 mm or more, about 0.9 mm or more) to about 1.5 cm (e.g., about 1.4 cm or less, about 1.3 cm or less, about 1.2 cm or less, about 1.1 cm or less, about 1 cm or less). For example, when the gap is circular, as shown in FIG. 1A, this dimension corresponds to the diameter of the circle (i.e., Ax=Ay), but non-circular (i.e., elliptical, polygonal, Ax≠Ay) gaps are also possible.

[0033] The transparent gap can subtend a solid angle in the viewer's field of view of about 30 degrees or less (e.g., about 25 degrees or less, about 20 degrees or less, about 15 degrees or less, about 12 degrees or less, about 10 degrees or less, about 9 degrees or less, about 8 degrees or less, about 7 degrees or less, about 6 degrees or less, about 5 degrees or less, about 4 degrees or less, about 3 degrees or less). The solid angles subtended at the horizontal and vertical viewing planes can be the same or different.

[0034] The dots are formed by an arrangement of bumps on the surface of each of the lenses 110a and 110b. The bumps are formed from an optically clear material with a refractive index similar to that of the underlying lens, 1.60 for polycarbonate. For example, in an embodiment where the lens is formed from polycarbonate, the bumps can be formed from a polymer with a similar refractive index to PC, such as a light-activated polyurethane or epoxy-based plastic. In addition to PC, the lens itself can also be made from allyl diglycol carbonate plastic, urethane-based monomers, or other impact-resistant monomers. Alternatively, the lens can be fabricated from one of the denser, higher refractive index plastics with a refractive index greater than 1.60.

[0035] In some embodiments, the ridge material is selected to have a refractive index that is within 0.1 (e.g., within 0.09 or less, 0.08 or less, 0.07 or less, 0.06 or less, 0.05 or less, 0.04 or less, 0.03 or less, 0.02 or less, 0.01 or less, 0.005 or less, 0.002 or less, 0.001 or less) of the refractive index of the lens material (e.g., measured at one or more wavelengths in the visible light range).

[0036] The protuberances are of a size and shape that allow the dots to scatter incident light and reduce the contrast of objects viewed in the contrast-reducing areas. The protuberances may be approximately spherical, ellipsoidal, or irregularly shaped. In general, the dimensions of the protuberances (e.g., the diameter shown in FIG. 1B) should be large enough to scatter visible light, but small enough so that they are not resolved by the wearer during normal use. For example, the protuberances can have dimensions (measured in the xy plane) ranging from about 0.001 mm or more (e.g., about 0.005 mm or more, about 0.01 mm or more, about 0.015 mm or more, about 0.02 mm or more, about 0.025 mm or more, about 0.03 mm or more, about 0.035 mm or more, about 0.04 mm or more, about 0.045 mm or more, about 0.05 mm or more, about 0.055 mm or more, about 0.06 mm or more, about 0.07 mm or more, about 0.08 mm or more, about 0.09 mm or more, about 0.1 mm or more) to about 1 mm or less (e.g., about 0.9 mm or less, about 0.8 mm or less, about 0.7 mm or less, about 0.6 mm or less, about 0.5 mm or less, about 0.4 mm or less, about 0.3 mm or less, about 0.2 mm or less, about 0.1 mm or less).

[0037] It should be noted that for smaller bumps, e.g., having dimensions comparable to the wavelength of light (e.g., 0.001 mm to about 0.05 mm), the scattering of light may be considered Rayleigh or Mie scattering. For larger bumps, e.g., about 0.1 mm or larger, the scattering of light may be due to the lensing effect of the bumps, e.g., due to focusing at a point well in front of the user's retina by a lens having a very small radius of curvature. In such cases, the light from each bump will be well away from its focus when it reaches the user's retina and will not be resolved into an image by the user.

[0038] In general, the dimensions of the ridges may be the same or different across each lens. For example, the dimensions increase or decrease as a function of the location of the ridges, e.g., measured from the transparent gap, and / or as a function of distance from the edge of the lens. In some embodiments, the dimensions of the ridges vary monotonically (e.g., monotonically increase or decrease) with increasing distance from the center of the lens. In some cases, the monotonically increasing / decreasing dimensions include linearly changing the diameter of the ridges as a function of distance from the center of the lens.

[0039] The bumps shown in FIG. 1B are arranged on a square grid and are uniformly spaced in each direction. y , D in the x direction xTypically the dots are spaced so that collectively they provide sufficient contrast reduction in the viewer's periphery for myopia relief. Smaller dot spacing usually leads to greater contrast reduction (provided adjacent dots do not overlap or merge). Generally, Dx and Dy are in the range of about 0.05 mm (e.g., about 0.1 mm or more, about 0.15 mm or more, about 0.2 mm or more, about 0.25 mm or more, about 0.3 mm or more, about 0.35 mm or more, about 0.4 mm or more, about 0.45 mm or more, about 0.5 mm or more, about 0.55 mm or more, about 0.6 mm or more, about 0.65 mm or more, about 0.7 mm or more, about 0.75 mm or more) to about 2 mm (e.g., about 1.9 mm or less, about 1.8 mm or less, about 1.7 mm or less, about 1.6 mm or less, about 1.5 mm or less, about 1.4 mm or less, about 1.3 mm or less, about 1.2 mm or less, about 1.1 mm or less, about 1 mm or less, about 0.9 mm or less, about 0.8 mm or less). As examples, the dot spacing may be 0.55 mm, 0.365 mm, or 0.240 mm.

[0040] The bumps illustrated in FIG. 1B are equally spaced in the x and y directions, but more typically the spacing in each direction may vary. Furthermore, the bumps may be arranged in a non-square grid. For example, a hexagonal grid may be used. Non-regular arrangements are also possible, for example, a random or semi-random dot arrangement may be used. The predetermined dimension in the case of a random pattern is the average spacing of the dots in the X and Y directions.

[0041] Although the dots are illustrated in FIG. 1B as having a circular footprint, more generally, the dots can have other shapes. For example, the dots may be elongated in one direction (e.g., in the x or y direction), such as in the case of elliptical dots. In some embodiments, the shape of the dots is random.

[0042] It is believed that light from the scene that enters the lens between the dots in the contrast reduction areas 130a and 130b will provide an image of the scene to the user's retina, while light from the scene that enters the dots will not. Furthermore, light that enters the dots is still transmitted to the retina, thus having the effect of reducing the contrast of the image without significantly reducing the luminosity at the retina. Thus, the contrast reduction in the user's peripheral vision is related (e.g., approximately proportional) to the percentage of the surface area of ​​the contrast reduction area that is covered by the dots. In general, the dots occupy at least 10% (e.g., 20% or more, 30% or more, 40% or more, 50% or more, e.g., 90% or less, 80% or less, 70% or less, 60% or less, etc.) of the area (measured in the xy plane) of the contrast reduction areas 130a and 130b.

[0043] Typically, the dot pattern reduces the contrast of the image of an object in the wearer's peripheral vision without significantly impairing the viewer's visual acuity in this area. Peripheral vision refers here to the visual field outside the field of view of the transparent gap. The image contrast in these areas is reduced by 40% or more (e.g., 45% or more, 50% or more, 60% or more, 70% or even 80% or more) with respect to the contrast of the image seen using the transparent gap of the lens being measured. The contrast reduction can be set according to the needs of each individual case. A normal contrast reduction is considered to be within the range of about 50% to 55%. A contrast reduction lower than 50% may be used in very mild cases, while more predisposed subjects may require a contrast reduction of more than 55%. Peripheral visual acuity can be corrected to 20 / 30 or better (e.g., 20 / 25 or better, 20 / 20 or better) as determined by subjective refraction while achieving significant contrast reduction.

[0044] Here, contrast refers to the difference in luminance between two objects in the same field of view, and contrast reduction therefore refers to a change in this difference.

[0045] Contrast and contrast reduction can be measured in a variety of ways: In some embodiments, contrast is measured based on the brightness difference between different parts of a standard pattern, such as a black and white square checkerboard, obtained under controlled conditions through transparent gaps and dot patterns in a lens.

[0046] Alternatively or additionally, contrast reduction can be determined based on the optical transfer function (OTF) of the lens (see, for example, http: / / www.montana.edu / jshaw / documents / 18%20EELE582_S15_OTFMTF.pdf). For the OTF, contrast is specified for the transfer of stimuli in which light and dark regions are sinusoidally modulated with different "spatial frequencies". These stimuli appear as alternating light and dark bars with the spacing between the bars varying over a range. For all optical systems, contrast transfer is lowest for sinusoidally varying stimuli with the highest spatial frequency. The relationship that describes the transfer of contrast for all spatial frequencies is the OTF. The OTF is obtained by taking the Fourier transform of the point spread function. The point spread function is obtained by imaging a point source through a lens onto a detector array and determines how the light from the point is distributed to the detectors.

[0047] When measurement discrepancies occur, the OTF technique is preferred.

[0048] In some embodiments, the contrast is estimated based on the percentage of the area of ​​the lens covered by the dots compared to the area of ​​the transparent gaps. In this approximation, it is assumed that all the light that hits the dots is uniformly distributed over the entire retinal area, reducing the amount of light available in the brighter areas of the image and adding light to the darker areas. Thus, the contrast reduction can be calculated based on the light transmission measured through the transparent gaps and the dot pattern of the lens.

[0049] Typically, the ophthalmic lenses 110a and 110b are clear or tinted. That is, the lenses are optically transmissive to all visible wavelengths and appear clear and / or colorless, or include spectral filters and appear colored. For example, the ophthalmic lenses may include filters that reduce the amount of red light transmitted to the wearer. It is believed that overstimulation of the L cones in the human eye (especially in children) results in suboptimal axial length elongation and myopia. Thus, using ophthalmic lenses to spectrally filter red light may further reduce the wearer's myopia.

[0050] Spectral filtering may be provided by applying a film to the surface of the lens. The film may be applied by physically depositing a material onto the lens surface, coating a layer of material onto the surface, or laminating a preformed film onto the surface. Suitable materials include absorbing filter materials (e.g., dyes), or multi-layer films to provide interference filtering. In some embodiments, spectral filtering may be achieved by including filtering materials in the lens material itself and / or in the material used to form the ridges.

[0051] 2, the effect of spectral filtering and contrast reduction from a dot pattern is illustrated by viewing black text on a white background using glasses 210. The white background against which the text is viewed is made to appear green by the glasses filtering out red wavelengths. Image contrast is unaffected at the transparent gaps 220a and 220b, but is reduced elsewhere in the viewer's visual field.

[0052] In general, dots can be formed from the lens in a variety of ways, including UV LED substrate direct printing, pad printing, hot stamping, and screen printing techniques. In some embodiments, the dots are formed by inkjetting a curable material onto the surface of a plain ophthalmic lens and curing the material to set the dot pattern. Referring to FIG. 3A, an inkjet and curing system 300 includes an inkjet printer 320 and a computer 310 in communication with the printer. The printer 320 includes a controller 330, a reservoir 340, an inkjet printhead 350, and a stage 360. The stage 360 ​​supports the lens 301 and positions the lens relative to the printhead 350. The reservoir 340 stores uncured material for inkjetting. Examples of curable materials suitable for inkjetting include a variety of commercially available proprietary monomers and oligomers crosslinked together by photopolymerization.

[0053] During operation, the print head 350 receives uncured material from the reservoir 340 .

[0054] Stage 360 ​​moves lens 301 relative to print head 350 (as illustrated by arrow 361), while print head 350 ejects droplets of uncured material 302 onto the lens. Either the stage and / or the print head can be the moving parts in this process. Depending on the size of the bumps desired, the volume of the droplets varies. The droplet volumes are within the range of 0.001 mm. 3 from 0.015mm 3 (For example, about 0.002 mm 3 , about 0.003 mm 3 , approx. 0.004 mm 3 , about 0.005mm 3 , approx. 0.006 mm 3 , approx. 0.008 mm 3 , about 0.010mm 3 , approx. 0.012 mm 3, ). Upon contacting the lens surface, the droplets wet the surface and form uncured ridges 305. Alternatively, in some embodiments, the stage 360 ​​is fixed while an actuator moves the print head relative to the lens.

[0055] System 300 also includes a UV lamp 370. Stage 360 ​​positions a lens adjacent to lamp 370 to enable the lamp to cure the deposited material to form the final bumps. Examples of suitable UV lamps include LEDs that emit wavelengths in the range of 360-390 nm.

[0056] A controller 330 communicates with the reservoir 340, print head 350, stage 360, and UV lamp 370 to coordinate the operation of each to facilitate the printing and curing of the drops. In particular, the controller 330 controls the relative movement between the print head 350 and stage 360, the inkjet drop ejection frequency, and the drop volume to enable the system 300 to form the desired dot pattern on the lens 301. The controller 330 also controls the temperature of the uncured material (e.g., by a heater associated with the reservoir 340 or elsewhere) to control the viscosity of the uncured material. A user inputs the drop pattern through the computer 310, which generates corresponding control signals for the printer and transmits the signals to the controller 330.

[0057] Commercially available inkjet printers may be used. Suitable inkjet printers include Roland DGA, Irvine, Calif., and Mimaki brand UV LED direct-to-substrate printers, Suwanee, Ga.

[0058] Ink-jetting the dot pattern allows an eye care professional to personalize the dot pattern for a patient in an inexpensive and efficient manner. Referring to FIG. 3B, personalized eyeglasses are provided by an order 380 that may all be performed in the eye care professional's office. In a first step 381, the eye care professional determines the patient's prescription, for example by refracting a subject. This step determines the power of the ophthalmic lens in which the dot pattern will be formed. The patient also selects the frames for their eyeglasses, just as they would for standard prescription eyeglasses.

[0059] In the next step 382, ​​the eye care professional selects an appropriate dot pattern for the patient. Parameters for the dot pattern that can be varied include, for example, the size of the dots, the density of the dots, the size and shape of the clear gaps, and the location of the clear gaps in the lens. Each of these can be individualized by the amount of contrast reduction in peripheral vision desired and the angular range of the clear gaps. An exemplary dot pattern is shown in FIG. 3C. This pattern prints dots over a larger area than most lens blanks, ensuring that the lens surface is completely covered by the dot pattern. Commercially available software suitable for generating images (e.g., Microsoft Office products such as Visio, PowerPoint, or Word) may be used in conjunction with standard inkjet driver software to generate control signals for the inkjet printer. Alternatively, special software may be used by the eye care professional to input the selected parameters for the pattern into the inkjet printer's computer.

[0060] Next, in step 383, an inkjet printer deposits droplets of uncured material to form dots in the desired pattern according to signals from a computer. The printed pattern is then exposed to curing radiation in step 384. In some embodiments, the center of the dot pattern, such as a transparent center, is aligned with the optical center of the lens. This can be done, for example, by measuring and marking the optical center using a lens measurement instrument, and aligning the printed pattern with the marked optical center. In one implementation, the optical center of the lens is first marked and outlined in a circle so that the optical center is aligned with the geometric center of the circular lens. Then, droplets are printed on the lens so that the dot pattern is centered in the circular lens, now coinciding with the optical center. Alternatively or additionally, a lens blank can be fabricated or selected such that the optical center always coincides with the geometric center of the lens.

[0061] Finally, in step 385, the lenses are framed and attached to the frame.

[0062] In some implementations, the lens is mounted in a frame and the frame is worn on the wearer before the dots are cured. In this manner, the printed dot pattern can be washed off the lens and reprinted if necessary.

[0063] Referring to FIG. 3D, in some implementations, a jig 390 is used to support multiple lens blanks during lens production. The jig 390 includes a tray 391 that features an array of lens holders 392 on one surface, each sized to securely hold a lens. For example, if 60 mm diameter lens blanks are used, the lens holders are each 60 mm in diameter to securely hold a respective lens. During operation, the jig 390 with one or more lenses is placed on the stage 360. The jig holds each lens in a precise position so that the system 300 can precisely jet the lens surface. Additionally, the jig allows multiple lenses to be produced per batch. Although the jig in FIG. 3D has 48 lens holders, in general the jig can be designed to hold any number of lenses, subject to the physical limitations imposed by the inkjet system. There can be many sizes of fixtures, such as fixtures that accommodate about 24 lenses, about 48 lenses, about 100 lenses, about 200 lenses, about 300 lenses, about 400 lenses, about 500 lenses, or more than 500 lenses per run.

[0064] Figures 4A-4C show photographs of a lens printed using the pattern of Figure 3C. Figure 4A shows the entire lens, while Figures 4B and 4C show enlarged portions of the dot pattern, with the portion of Figure 4C including the transparent gaps.

[0065] Other methods for forming the bumps are also possible. For example, instead of inkjet, transfer or lithographic printing can be used. Transfer printing involves forming the bumps on a different substrate and transferring them to the surface of the lens in a separate process step. Lithographic printing involves forming a continuous uniform layer of bump material on the lens surface and patterning the layer to form a dot pattern. Optical or contact lithography can be used to pattern the layer. Alternatively, the bumps may be molded into the lens surface using the same molding process used to form the lens. In this case, the bumps are part of the lens mold. In some embodiments, the dot pattern may be provided by a film that is laminated to the surface of the lens.

[0066] Although the dot patterns in the above embodiments are protuberances formed on the surface of the ophthalmic lens, other implementations that provide comparable optical properties and lens durability are possible. For example, in some embodiments, the contrast reduction is provided by an array of recesses in the lens surface. The recesses can have dimensions similar to the protuberances described above. The recesses can be formed using a variety of techniques, such as etching (e.g., physical or chemical etching) or removing material from the lens surface (e.g., using a laser beam, molecular beam, or ion beam). In some embodiments, the recesses are formed during molding of the lens.

[0067] Alternatively or additionally, the dot pattern may be incorporated into the lens material itself, for example by dispersing appropriately sized transparent beads, with refractive indices different between the bead material and the bulk lens material, into the lens material as the lens is being molded, with transparent gaps being formed solely in the bulk lens material.

[0068] In some embodiments, the contrast reduction is provided by other diffusing structures, such as rough surfaces. Holographic diffusers or ground glass diffusers may be used. In some embodiments, the diffuser may be provided by a film laminated to the surface of the lens.

[0069] Although the above description relates to spectacle ophthalmic lenses, the principles disclosed may be adapted to other forms of ophthalmic lenses, such as contact lenses. In some embodiments, a dot pattern is formed on the contact lens to provide a similar therapeutic effect. The size and spacing of the dot pattern on the contact lens subtends a solid angle in the user's field of vision comparable to the dot patterns described above with respect to spectacle lenses.

[0070] The dot pattern can be formed on the contact lens in a variety of ways. For example, the dot pattern can be printed or transferred onto the contact lens surface using the techniques described above. Alternatively, the dot pattern can be formed by spraying the contact lens with scattering material.

[0071] In some embodiments, dots are formed on one or both sides of a contact lens by exposing the contact lens surface to a laser beam. The laser beam locally removes the contact lens material at the surface, leaving small depressions. By selectively exposing the contact lens surface to the laser beam, a dot pattern can be formed on the surface. For example, the beam of the laser can be moved relative to the surface while the beam is pulsed. Relative motion between the beam and the contact lens surface can be achieved by moving the beam while the surface is fixed, by moving the surface while the beam is fixed, or by moving both the beam and the surface.

[0072] 13, a laser system 1300 for forming dots on a lens surface includes a laser 1320, a beam chopper 1330, focusing optics 1340, a mirror 1350, and a stage 1370. The laser 1320 directs a laser beam to the mirror 1350, which deflects the beam toward a contact lens 1301 that is positioned relative to the mirror 1350 by the stage 1370. An actuator 1360 (e.g., a piezoelectric actuator) is attached to the mirror 1350. The stage includes a curved mounting surface 1380 that supports the contact lens 1301. The laser system 1300 also includes a controller (e.g., a computer controller) in communication with the laser 1320, the beam chopper 1330, and the actuator 1360.

[0073] A beam chopper 1330 and focusing optics 1340 are located in the beam path. The chopper 1330 periodically blocks the beam, allowing the contact lens 1301 to be exposed to individual pulses of the laser beam. The focusing optics 1340, which typically includes one or more optically actuated elements (e.g., one or more lenses), focuses the beam to a spot on the surface of the contact lens 1301 that is small enough so that the area removed by the beam matches the desired dot size. An actuator 1360 redirects a mirror 1350 relative to the beam to scan the pulsed beam to different target points on the contact lens surface. A controller 1310 coordinates the operation of the laser 1320, chopper 1330, and actuator 1360 such that the laser system forms a predefined dot pattern on the contact lens.

[0074] In some embodiments, the stage 1370 also includes an actuator. The stage actuator may be a multi-axis actuator, for example, moving the contact lens in two lateral dimensions perpendicular to the light propagation direction. Alternatively or additionally, the actuator may move the stage along the light beam direction. Moving the stage along the light beam direction is used to keep the exposed portion of the lens surface at the focal point of the light beam, regardless of the curvature of the lens surface, thereby maintaining a nearly constant dot size across the lens surface. The stage actuator is also controlled by a controller 1310, which coordinates this stage movement with other elements of the system. In some embodiments, a stage actuator is used in place of a mirror actuator.

[0075] In general, the laser 1320 can be any type of laser capable of generating light with sufficient energy to remove contact lens material. Gas lasers, chemical lasers, dye lasers, solid-state lasers, and semiconductor lasers can be used. In some embodiments, an infrared laser, such as a CO2 laser (having an emission wavelength of 9.4 μm or 10.6 μm), can be used. For example, a commercially available laser system, such as a CO2 laser system (e.g., a 60W VLS 4.60 system) manufactured by Universal Laser Systems, Inc. of Scottsdale, Arizona, can be used.

[0076] The pulse width and pulse energy are typically selected to remove a certain amount of material from the contact lens surface to form dots of a desired size. An example of a dot pattern for a contact lens is shown in FIG. 14A, where contact lens 1400 includes a transparent gap 1410, a contrast-reduction region 1420, and a transparent outer region 1430. Contrast-reduction region 1420 is an annular region having an inner diameter ID and an outer diameter OD. ID corresponds to the diameter of transparent gap 1410. The contact lens has a lens diameter LD that is greater than OD.

[0077] Generally, ID is smaller than the diameter of the user's pupil under normal room lighting conditions (e.g., general classroom or office lighting where the user can easily read the text of a book). This ensures that image contrast in the user's peripheral vision is reduced under such lighting conditions. In some embodiments, ID is in the range of about 0.5 mm to about 2 mm (e.g., in the range of about 0.75 mm to about 1.75 mm, in the range of about 0.9 mm to about 1.2 mm, about 0.6 mm or more, about 0.7 mm or more, about 0.8 mm or more, about 0.9 mm or more, about 1 mm or more, about 1.1 mm or more, about 1.2 mm or more, about 1.9 mm or less, about 1.8 mm or less, about 1.7 mm or less, about 1.6 mm or less, about 1.5 mm or less, about 1.4 mm or less, about 1.3 mm or less).

[0078] Typically, the OD is large enough so that the contrast-reducing region extends beyond the user's pupil under normal room lighting conditions, and in some embodiments, the OD is about 2.5 mm or more (e.g., about 3 mm or more, about 4 mm or more, about 5 mm or more, e.g., about 10 mm or less, about 8 mm or less, about 7 mm or less, about 6 mm or less, etc.).

[0079] In general, the size and spacing of the dots on the contact lens are selected to produce the desired optical effect (e.g., as described above) and are limited by the method used to form the dots. In some embodiments, the dots may have a maximum lateral dimension of about 0.005 mm or more (e.g., about 0.01 mm or more, about 0.015 mm or more, about 0.02 mm or more, about 0.025 mm or more, about 0.03 mm or more, about 0.035 mm or more, about 0.04 mm or more, about 0.045 mm or more, about 0.05 mm or more, about 0.055 mm or more, about 0.06 mm or more, about 0.07 mm or more, about 0.08 mm or more, about 0.09 mm or more, about 0.1 mm) to about 0.5 mm or less (e.g., about 0.4 mm or less, about 0.3 mm or less, about 0.2 mm or less, about 0.1 mm).

[0080] The spacing of the dots can also be varied to produce the desired optical effect. Typically, the spacing of the dimples (i.e., measured between the centers of adjacent dimples) ranges from about 0.05 mm (e.g., about 0.1 mm or more, about 0.15 mm or more, about 0.2 mm or more, about 0.25 mm or more, about 0.3 mm or more, about 0.35 mm or more, about 0.4 mm or more, about 0.45 mm or more) to about 1 mm (e.g., about 0.9 mm or less, about 0.8 mm or less, about 0.7 mm or less, about 0.6 mm or less, about 0.5 mm or less).

[0081] The relative areas of the dots in the contrast-reduced regions may vary as described above for spectacle lenses.

[0082] The LD corresponds to the diameter of the contact lens and is usually in the range of about 10-20 mm. Generally, the LD is at least 1 mm larger than the OD (e.g., about 2 mm or more, about 3 mm or more, about 4 mm or more, about 5 mm or more, about 6 mm or more, about 7 mm or more, about 8 mm or more). Including at least some margin of white space around the edge of the contact lens that does not include the dots ensures that the dots do not reduce the quality of the contact lens at its edge (e.g., by tearing) or reduce the integrity of the seal between the contact lens and the wearer's eye.

[0083] The dot pattern of the contact lens shown in Figure 14A features dots that are each the same size and have the same spacing between adjacent dots, although other dot arrangements are possible. For example, referring to Figure 14B, contact lens 1450 features dots of various sizes. Here, contact lens 1450 includes transparent gap 1460, contrast reduction region 1470, and transparent outer region 1480. Contrast reduction region 1470 includes a dot pattern in which the dot size increases as the radial distance of the dot location increases relative to the center of the lens. Thus, dot 1471 closest to transparent gap 1460 is the smallest and dot 1472 closest to outer region 1480 is the largest.

[0084] Although system 1300 is shown as removing contact lenses, more generally, laser ablation can also be used on eyeglass lenses.

[0085] Although myopia progression and treatment are observed in subjects using various techniques (e.g., subjective refraction and / or axial length measurement), choroidal thickness change (i.e., choroidal thickness increase) is considered to be a reliable biomarker for this purpose. Choroidal thickness can be measured using optical coherence tomography (OCT). Exemplary deep OCT images showing the choroidal thickness of a subject are shown in Figures 5A and 5B. The choroid is shown in cross section between two yellow curves, spanning the image from left to right. Since OCT images have variable magnification, internal landmarks, whose thickness does not change over the course of treatment, can be used as a reference when measuring thickness. An example of such a landmark is the retinal pigment epithelium (RPE) layer between the choroid and the retina, the thickness of which is shown by the red line illustrated in Figure 5B. EXAMPLES

[0086] Initial research / comparative examples Previous studies have shown that proof-of-concept glasses using a diffusion filter attached to the lens surface can slow down the axial lengthening of subjects, but have presented many challenges. The filter used was a commercially available Bangerter Occlusion Foil ("BOF"). The diffuser was made of a thin, flexible, static vinyl film that was cut to match the lens shape and attached to the right lens. The "foil" used was "BOF-0.8 Visual Acuity 20 / 25" and, as the name suggests, reduced the nominal best corrected visual acuity to 20 / 25. However, in reality, subjects whose best corrected visual acuity ranged from 20 / 15 to 20 / 20 had visual acuity ranging from 20 / 30 to 20 / 40 with the BOF-0.8 filter. The subjects in this study wore a diffuser unilaterally in one eye because of the large decrease in vision it caused, and concerns about tolerance and safety of wearing glasses that reduced vision to 20 / 30-40 in both eyes. By making the diffuser group monocular, the subjects in this study were able to use one eye at high vision and function normally. Ideally, however, in a commercially available product, treatment should be given to both eyes simultaneously.

[0087] Another problem in the initial studies was that the vinyl filters could accidentally come off the lenses. To address this issue, each subject in the study was provided with two pairs of glasses and instructed to use the second pair if the filter came off the first pair, and it was possible to provide subjects with a new spare pair. Ideally, in a commercial product, the diffuser should be as durable as the standard lenses.

[0088] new research Prototype lenses were designed to address the issues with the glasses used in the earlier study while maintaining or improving their effectiveness in slowing down axial elongation. It is believed that the main reason the BOF-0.8 filter reduced visual acuity so dramatically is because the optical quality of the vinyl film itself is very poor. The uneven thickness created a "wavy" pattern that distorted the image and made vision difficult. However, this degradation of the image was not believed to have any therapeutic value. Thus, one goal of the prototype lenses in the new study was to eliminate any type of film attached to the glasses and to have a diffuser as a permanent part of the lens itself. In the new design, the diffuser component of these lenses serves the purpose of reducing the contrast of the image, but all other aspects of the optical quality are essentially the same as the standard of care.

[0089] The first step in the development of the glasses was to produce a lens that would reproduce the amount of diffusion (and presumably the therapeutic value) of the BOF-0.8 filter, but have all the other optical properties of a standard (i.e., non-diffusing) lens. The efficacy of the new prototype was compared to the BOF-0.8 filter from the earlier study, which was used as a baseline for efficacy. To reduce the length of the new prototype study, choroidal thickness, measured using optical coherence tomography (OCT), was used as a biomarker of therapeutic efficacy. The choroid was imaged using OCT, demonstrating that the BOF-0.8 filter produces accurately measured choroidal thickness. Images obtained in this study are shown in Figure 6A-D. OCT noninvasively yields a cross-sectional view of the retina through the fovea. Multiple layers can be resolved, including the inner limiting membrane nerve fiber layer (NFL), ganglion cell layer (GCL), inner plexiform layer (IPL), inner nuclear layer (INL), inner / outer photoreceptor segment junction (IS / OS PR), outer nuclear layer (ONL), and retinal pigment epithelium (RPE). The deepest layer is the choroid. Figures 6A and 6C show unsegmented images of the retina of one subject before and after treatment with a BOF-0.8 filter. The relative thickness of the choroidal layers is evident after treatment compared to before treatment. Figures 6B and 6D include a division line (red) indicating the outer border of the choroid. Figure 6C shows the choroid 39 days after treatment. Figure 6D shows the choroid 39 days after treatment with the outer border of the choroid defined. Thickness was measured as the distance from the border to the RPE border.

[0090] Figure 7 shows a plot of relative choroidal thickness as a function of location in the retina for this study. The marked post-treatment choroidal thickness (upper, blue curve) is evident across the retina compared to the pre-treatment measurements (lower, black curve).

[0091] Example: Prototype I The first prototype glasses, Prototype I, were developed to incorporate a diffusing element to provide a lens that would reduce image contrast by substantially the same amount as the BOF-0.8 filter, while being practical and durable, and without many of the optical defects found in the vinyl substrate of the BOF-0.8 filter. The lenses were created by inkjet printing a dot pattern onto the lens using a UV-curable material. Both Roland DG's VersaUV line of inkjet printers and Mimaki's UV flatbed printer printers were used on the different versions of Prototype I. UV-curable materials were also sourced from Roland and Mimaki.

[0092] The lens is a clear polycarbonate shatterproof lens with no spectral filtering. The dot pattern was printed on a square grid with 0.55 mm spacing. The dot volume was 0.004 mm. 3 The dot pattern covered the entire lens, leaving no transparent gaps. The printed pattern was cured using a UV LED emitting in the range of 365nm to 385nm. A photo of an example of a Prototype I lens is shown in Figure 8.

[0093] We tested the prototype I lens using a within-subject protocol. A small number of subjects were recruited and refracted to their best corrected visual acuity. The hypothesis that the initial decrease in axial length was the result of choroidal thickening was tested with an OCT study.

[0094] One week after the baseline measurements, subjects wore spectacles with an untreated left eye (OS) lens and a BOF-0.8 filter attached to the right eye (OD) lens. Then, four weeks later, subjects had the left eye (OS) replaced with a new prototype lens and the right eye wore an untreated lens. The absolute difference in choroidal thickness between the left and right eyes (OD-OS) increased significantly after one month of wearing the BOF-0.8 filter in the right eye. When the OD spectacles were removed and the OS eye was treated with prototype I, there was a corresponding significant decrease in the axial length of the OS (p=0.0083) and an increase in the OD-OS value (p=0.0032). There was no significant difference in efficacy between prototype I and the BOF-0.8 filter in producing an increase in choroidal thickness. However, there was a significant difference in best corrected visual acuity when wearing our prototype I compared to the BOF-0.8 filter.

[0095] Example 2: Prototype II The goal of Prototype II was to produce a lens that would allow a measured best corrected visual acuity of 20 / 15 to 20 / 20, but exhibit equal or better effectiveness than the BOF-0.8 filter. To achieve this goal, Prototype II was produced by modifying the dot pattern of Prototype I to incorporate a small central clear area. The dots were formed on a square grid pattern with spacing of 0.55 mm. The clear gaps were formed in circles with a diameter of 3.8 mm. A photograph of the Prototype II lens is shown in Figure 9.

[0096] When the glasses were worn, the clear area was positioned to coincide with the pupil so that the wearer looked through the clear area when looking straight ahead. Subjects who had a best correction of 20 / 15 to 20 / 20 achieved 20 / 15 to 20 / 20 when wearing Prototype II and reading an eye chart through the clear area.

[0097] We tested Prototype II with a clear region against Prototype I by recruiting a small number of subjects to wear a lens with a clear region in the left eye and a lens without a clear region in the right eye. We compared the choroidal thickness increase between the two eyes and found no difference between the lenses with and without a clear region. This demonstrated that it is possible to design a diffuser lens without spectral filtering that allowed subjects to be tested with best corrected visual acuity of 20 / 15 to 20 / 20 and maintain the efficacy (as measured by choroidal thickness increase) of the original lens used in the initial study.

[0098] Example 3: Prototype III Further refinements were investigated to simultaneously maximize tolerability and efficacy. We believed that a larger clear area would make the prototype better tolerated, but we hypothesized that increasing the peripheral contrast reduction might also increase efficacy. Thus, we experimented with these two values ​​to produce one more prototype: Prototype III. Like Prototypes I and II, Prototype III had no spectral filtering. The dot pattern in Prototype III was modified to include larger clear gaps and greater contrast reduction outside the clear areas than Prototype II. Specifically, the clear gaps were enlarged to 5.0 mm in diameter and the square grid spacing was reduced to 0.365 mm. The dot size remained the same as Prototype II. A photograph of the Prototype III lens is shown in Figure 10.

[0099] The design goal was to develop a prototype that would allow good visual acuity that would be satisfactory and comfortable for children and their parents. Visual acuity with Prototype III for children with best corrected visual acuity of 20 / 15 to 20 / 20 was 20 / 15 to 20 / 20 when visual acuity was tested while looking through the clear gap in the lens. We also tested "off-axis" visual acuity while subjects looked through the peripheral diffuser. Subjects with best corrected visual acuity of 20 / 15 to 20 / 20 through the clear gap exhibited visual acuity of 20 / 20 to 20 / 25 when looking through the diffuser area.

[0100] We started a small study with the prototype III worn in both eyes. The main purpose of the lens was to analyze the durability and tolerability of the lens. The study had one group. The subjects had a history of myopia progression from 7 to 10 years old. All subjects were referred to us by their ophthalmologists because their parents were concerned about the rapid myopia progression in their children. The study was a single-center, ophthalmology study at the University of Washington in Seattle. Eight children participated. Preliminary results were obtained on four children who had been wearing the glasses for six months, with axial length monitored with a Carl Zeiss Meditec IOL Master optical biometry device. The children were also asked to keep a diary recording how many hours per day they wore the lenses and noting any problems or concerns they had with the glasses.

[0101] When subjects came to the lab for axial length measurements, we examined their diaries to see if there were any signs of change or deterioration in their glasses. We also asked subjects and their parents if they had had any problems or concerns with the glasses. There were no significant issues with the durability of the glasses and no complaints from subjects or parents.

[0102] However, with reference to Figure 12, it is interesting to compare the axial length of subjects wearing Prototype III with the results at 6 months in the earlier study. This figure is a bar graph comparing the diopter change for the subjects' eyes after 180 days. The first bar represents the control glasses and the second bar represents the original diffuser glasses from the earlier study. The third bar represents Prototype III after 6 months for the four children who completed the 6-month study.

[0103] We have demonstrated that it is possible to produce stable, durable eyeglasses that enable 20 / 15 to 20 / 20 visual acuity. This small group of subjects was very satisfied with the eyeglasses and showed a slowing of progression after 6 months.

[0104] Example 4: Contact lenses The dot patterns were formed on the contact lenses as follows: In each case, a -7.5D contact lens was placed on a rolling bearing on the stage of a VLS4.60 CO2 laser system (Universal Laser Systems, Scottsdale, AZ). The lens diameter in each case was 14 mm.

[0105] The contact lenses were exposed at 5%, 10%, and 20% power settings, respectively. For each exposure, the laser scan speed was set to 25% and the resolution was set to 0.002 inches. The exposure field had an outer diameter of 12.7 mm and an inner diameter of 1 mm. The exposure pattern within the field was a square grid with a grid spacing of 0.0116 inches.

[0106] Visible dot patterns were produced for power settings of 5% and 10%. A power setting of 20% resulted in severing the contact lens.

[0107] A photograph of one of the contact lenses is shown in Figure 15A. The dot pattern is clearly visible.

[0108] Example 5: Eyeglass lenses using laser ablation Dot patterns were created on several Trivex eyeglass lenses using a 60 W, 10.6 μm VLS4.60 CO2 laser system (Universal Laser Systems, Scottsdale, AZ). The lenses were exposed to various powers between 5% and 40%, in both raster and vector print modes. The laser was set at 1000 PPI. Speed ​​settings were either 25% or 100%.

[0109] A photograph of the lens exposed in vector mode is shown in Figure 15B. The dot pattern in this example, printed in vector mode, is clearly visible.

[0110] A number of embodiments have been described. Other embodiments are within the scope of the following claims.

Claims

1. receiving a plain ophthalmic lens including a curved surface; forming a plurality of dots on the curved surface having a maximum dimension in the range of 0.025 mm to 1 mm and spaced apart by 0.8 mm or less, wherein for incident light transmitted by each ophthalmic lens, the ophthalmic lens scatters light incident on the plurality of dots; The method, wherein forming a plurality of dots on the curved surface comprises exposing the curved surface to laser radiation or depositing a material on the curved surface, the dots being comprised of the deposited material.

2. The method of claim 1 , wherein depositing a material on the curved surface comprises printing a material on the curved surface.

3. The method of claim 2 , wherein the material is inkjet printed on the curved surface.

4. The method of claim 1 , wherein forming a plurality of dots on the curved surface comprises curing the material after depositing the material on the curved surface.

5. The method of claim 4 , wherein the material is cured using radiation or heat.

6. The method of claim 1 , wherein exposing the curved surface to laser radiation comprises exposing the curved surface to individual pulses of laser radiation.

7. The method of claim 1 , wherein exposing the curved surface to laser radiation comprises scanning the curved surface with a laser beam.

8. The method of claim 1 , wherein exposing the curved surface to laser radiation comprises removing lens material from the curved surface.

9. The method of claim 1 , wherein the spacing between adjacent dots varies across the curved surface.

10. The method of claim 1 , wherein the dots are arranged in a random pattern.

11. The method of claim 1 , wherein the dots are arranged on a grid.

12. The method of claim 1 , wherein the dots comprise bumps on the curved surface.

13. The method of claim 1 , wherein the dots comprise indentations on the curved surface.

14. The method of claim 1 , wherein the ophthalmic lens is a spectacle lens.

15. The method of claim 1 , wherein the ophthalmic lens is a contact lens.

16. The method of claim 1 , wherein the ophthalmic lens is made from polycarbonate.

17. The method of claim 1 , wherein the ophthalmic lens is fabricated from a material having a refractive index greater than 1.60.

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