Ophthalmic lens with light scattering for treating myopia and method of making same

Abstract

Ophthalmic lenses for reducing myopia progression are disclosed, including scattering centers with reduced back scattering, including various shapes and patterns of scattering centers. A method for manufacturing an ophthalmic lens and an apparatus comprising an ophthalmic lens are disclosed.

Description

Technical Field

[0001] The present invention is characterized by ophthalmic lenses for treating myopia and reducing the progression of myopia, and a method for manufacturing the same. Background Technology

[0002] The eye is an optical sensor in which light from an external source is focused through the lens onto the surface of the retina, i.e., onto an array of wavelength-dependent light sensors. Each of the various shapes the lens can take is associated with a focal length at which external light is optimally or nearly optimally focused to produce an inverted image on the surface of the retina corresponding to the external image observed by the eye. A lens of each of the various shapes it can take optimally or nearly optimally focuses light emitted or reflected by external objects located within a certain distance range from the eye, and less optimally or fails to focus on objects located outside that distance range.

[0003] In individuals with normal vision, the axial length of the eye, or the distance from the lens to the surface of the retina, corresponds to the near-optimal focal length for focusing on distant objects. The eye of an individual with normal vision focuses on distant objects without nerve input to the muscles—that is, the muscles exert force to change the shape of the eye's lens—a process known as "accommodation." Nearer, more immediate objects are then focused by the individual as a result of accommodation.

[0004] However, many people suffer from eye length-related impairments, such as myopia (“nearsightedness”). In nearsighted individuals, the axial length of the eye is longer than the axial length required to focus on distant objects without accommodation. As a result, nearsighted individuals can see nearby objects clearly, but more distant objects are blurry. While nearsighted individuals are generally able to accommodate, they are able to focus on objects at an average distance shorter than the average distance of individuals with normal vision.

[0005] Typically, infants are born farsighted, with eye lengths shorter than those required for optimal or near-optimal focusing of distant objects without accommodation. During normal eye development, known as "emmetropization," the axial length of the eye relative to the rest of the eye increases to provide near-optimal focusing of distant objects without accommodation. Ideally, as the eye grows to its final adult size, biological processes maintain a near-optimal relative eye length to eye size. However, in myopic individuals, the relative axial length of the eye to its overall eye size continues to increase during development, exceeding the length required for near-optimal focusing of distant objects, leading to increasingly pronounced myopia.

[0006] Myopia is believed to be influenced by both behavioral and genetic factors. Accordingly, treatment devices that address behavioral factors can help reduce myopia. For example, U.S. Patent Publication No. 2011 / 0313058A1 describes a treatment device for treating eye length-related disorders, including myopia. Summary of the Invention

[0007] Eyeglasses that reduce the signals in the retina responsible for eye length growth are disclosed. Example eyeglass lenses are made using, for example, polycarbonate or Trivex lens blanks that have been treated by forming a pattern of scattering centers or “dots,” alternatively having a dot-free aperture on the viewing axis. Dots scatter incident light that would otherwise be focused by the lens, resulting in reduced contrast in the retinal image. Reduced contrast reduces eye growth associated with myopia development, especially in children. The optional dot-free aperture is typically located on the visual axis corresponding to the wearer's distance vision and allows the user to experience maximum visual acuity when viewing objects on the axis, while objects at the periphery of the user's field of vision are viewed with reduced contrast and acuity.

[0008] Controlling the size and shape of the dots is used to adjust the light scattering properties of the lens. One function is to increase forward scattering in the direction in which scattered light contributes to reduced image contrast in the wearer's peripheral field of vision. Another function is to reduce backscattered light. Reducing backscattered light reduces the conspicuousness of the dot pattern. Increased directional forward scattering reduces the overall number of dots needed to provide a therapeutic effect.

[0009] A laser exposure method for forming dot-like objects with desired shapes is also disclosed. The exposure method can include using an efficiently achievable laser scanning path, increasing the overall throughput of the laser system by reducing the exposure time or cycle time.

[0010] Among other advantages, the disclosed embodiments are characterized by eyeglasses that include features that reduce the signal in the retina responsible for eye length growth on the lens of both eyes without reducing the user's on-axis vision in either eye to a degree that would be detrimental to the user. For example, a dot pattern that allows viewing through a clear aperture on the normal axis allows for all-day, daily use while providing a moderate blurring of the wearer's peripheral vision or a reduction in contrast. Compared to methods involving the alternating use of different pairs of eyeglasses, the disclosed embodiments are also able to provide therapeutic benefits to the user in both eyes using only a single pair of eyeglasses.

[0011] Furthermore, dot patterns can be largely inconspicuous to others, especially when the dot pattern is clear and colorless and / or when using contact lenses. The subtlety of dot patterns can lead some wearers, particularly children, to continue using them more frequently, as these wearers might otherwise feel uncomfortable using more conspicuous devices in daily life (e.g., at school or among peers). For example, graded dot patterns can be used to reduce the conspicuousness of the dot pattern to third parties.

[0012] The disclosed embodiments enable the efficient and economical formation of dot patterns for mitigating eye elongation on conventional ophthalmic lenses, for example, by forming dot patterns on the surface or in the body of the lens. Attached Figure Description

[0013] Figure 1A An example pair of glasses is shown, containing ophthalmic lenses designed to reduce the development of myopia.

[0014] Figure 1B shows the process before edge grinding. Figure 1A The ophthalmic lens shown.

[0015] Figure 1C A plan view of the dot pattern in the area of ​​reduced contrast of the lens shown in Figure 1B is presented.

[0016] Figure 2 This is a schematic diagram showing light scattering from the ophthalmic lens shown in Figure 1B.

[0017] Figure 3A A cross-sectional view of an example dot-like structure consisting of depressions in the surface of a lens is shown.

[0018] Figure 3B A cross-sectional view of an example dot-like structure consisting of protrusions on the surface of a lens is shown.

[0019] Figure 3C A cross-sectional view of another example of a dot-like structure consisting of depressions in the surface of a lens is shown.

[0020] Figure 3D A cross-sectional view of another example of a dot-like structure consisting of depressions in the surface of a lens is shown.

[0021] Figures 4A to 4S A plan view of the perimeter path of an example point is shown.

[0022] Figure 5A It is a drawing that compares the number of light rays hitting the retina for five different simulated point shapes.

[0023] Figure 5BIt is a drawing that compares the number of backscattered rays for five different simulated point shapes.

[0024] Figure 6 This is a schematic diagram of an example laser system used to form dots on the surface of a lens.

[0025] Figure 7 This is a plan view of an example laser irradiation path used to form point-like objects.

[0026] Figure 8 This is a plan view of another example laser irradiation path used to form dot-like objects.

[0027] Figure 9A Is using Figure 8 A top view of the image of the two point-like objects formed by the path shown.

[0028] Figure 9B yes Figure 9A The cross-sectional profile of one of the point-like objects shown.

[0029] Figure 10A Is using Figure 7 A top view of the image of the two point-like objects formed by the path shown.

[0030] Figure 10B yes Figure 10A The cross-sectional profile of one of the point-like objects shown.

[0031] Figure 11A This is a plan view of an example laser irradiation path used to form point objects with discrete laser radiation pulses along the path.

[0032] Figure 11B Is using Figure 11A A top view of the image of the two point-like objects formed by the path shown.

[0033] Figure 11D is Figure 11B The cross-sectional profile of one of the point-like objects shown.

[0034] Figure 12A shows an example dot pattern on an ophthalmic lens with dots generated by laser burning.

[0035] Figure 12B is a magnified view of a portion of the dot pattern in Figure 12A.

[0036] Figure 12C This is an enlarged cross-sectional view of the point-like object taken at point CC in Figure 12B.

[0037] Figure 13 It is a flowchart of a method for forming dot-like objects using a laser system with a laser for forming grooves.

[0038] Figure 14 Example dot patterns with different sizes are shown.

[0039] Figure 15 Another example dot pattern with dots of different sizes is shown.

[0040] Figure 16 Another example dot pattern with dots of different sizes is shown.

[0041] Figure 17 An example dot pattern with overlapping dots is shown.

[0042] Figure 18 An example dot pattern with rows of overlapping dots is shown.

[0043] Figure 19 Another example dot pattern with rows and columns of overlapping and non-overlapping dots is shown.

[0044] Figure 20 Another example dot pattern is shown, depicting a radial array of overlapping dots of varying sizes.

[0045] Figure 21 Another example dot pattern with overlapping and non-overlapping dots of varying sizes and radial array is shown.

[0046] Figure 22 Another example dot pattern with overlapping and non-overlapping dots of varying sizes is shown.

[0047] In the accompanying drawings, the same reference numerals denote the same elements. Detailed Implementation

[0048] refer to Figures 1A to 1C The diagram illustrates eyeglasses 100 for reducing the progression of myopia. Eyeglasses 100 treat both eyes simultaneously without substantially impairing the wearer's axial clarity. Furthermore, the eyeglasses are sufficiently secure and inconspicuous to allow the wearer to participate in the same daily activities without malfunctioning and without feeling uncomfortable with their appearance, which is particularly desirable since eyeglasses are typically used to inhibit eye elongation in children.

[0049] The eyeglasses 100 consist of a frame 101 and ophthalmic lenses 110a and 110b mounted in the frame 101. Typically, the ophthalmic lenses can be plano lenses, single vision lenses (e.g., having positive or negative power), or multivision lenses (e.g., bifocal or progressive lenses). Each of the ophthalmic lenses 110a and 110b has a sharp aperture 120a and 120b, respectively surrounded by regions 130a and 130b with reduced contrast. The sharp apertures 120a and 120b can be positioned to correspond to the wearer's hyperopic vision, while the regions 130a and 130b with reduced contrast correspond to the wearer's peripheral field of vision, and the wearer's gaze direction corresponds to hyperopic vision. Lens 110a is shown as pre-ground in Figure 1B.

[0050] Typically, the size and shape of the clear apertures 120a and 120b can vary. Generally, the clear aperture provides the wearer with a cone of vision for which their visual acuity can be optimally corrected (e.g., 20 / 15 or 20 / 20). In some examples, the aperture has a maximum size ranging from about 0.2 mm (e.g., about 0.3 mm or greater, about 0.4 mm or greater, about 0.5 mm or greater, about 0.6 mm or greater, about 0.7 mm or greater, about 0.8 mm or greater, about 0.9 mm or greater) 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). In the case where the aperture is circular, for example, as... Figure 1A As shown in Figure 1B, this dimension corresponds to the diameter D of the circle. 120 However, non-circular (e.g., elliptical, polygonal, torn) holes are also possible.

[0051] A clear aperture allows for a solid angle of approximately 30 degrees or less (e.g., approximately 25 degrees or less, approximately 20 degrees or less, approximately 15 degrees or less, approximately 12 degrees or less, approximately 10 degrees or less, approximately 9 degrees or less, approximately 8 degrees or less, approximately 7 degrees or less, approximately 6 degrees or less, approximately 5 degrees or less, approximately 4 degrees or less, approximately 3 degrees or less) in the viewer's field of view. The solid angles facing each other in the horizontal and vertical viewing planes can be the same or different.

[0052] In some cases, lenses 110a and 110b are able to exclude areas of sharp aperture and reduced contrast that occupy the entire on-axis field of view.

[0053] Referring to Figure 1B, the region 130a of reduced contrast extends to a radius smaller than the radius of the pre-edge lens, occupying an annular region surrounding the clear aperture 120a. Typically, the region of reduced contrast of the pre-edge lens extends far enough to achieve the desired level of light scattering in the user's peripheral field of vision, regardless of the user's viewing direction when wearing the glasses, after the lens has been edged and mounted in frame 101. The region 130a of reduced contrast is capable of having a maximum size (e.g., in the case of a circular region, diameter D) ranging from about 3 cm to about 9 cm (e.g., about 4 cm or greater, about 5 cm or greater, about 6 cm or greater, about 7 cm or greater, such as about 8 cm or less). 130 While the area 130a with reduced contrast has a circular perimeter, other shapes are also possible (e.g., ellipse, polygon, etc.).

[0054] Special Reference Figure 1C The regions 130a and 130b with reduced contrast include scattering centers, also known as “dots” 112, which reduce the contrast of objects in the wearer’s peripheral vision by scattering light passing through those regions into the wearer’s eye. The lens region between the dots 140 corresponds to the original (e.g., Rx) lens surface that provides the wearer with a clear, focused image. The result of the regions 130 with reduced contrast is a resolvable image for the wearer that corrects for any refractive errors in the wearer, with a reduced level of contrast compared to the on-axis image viewed through clear apertures 120a and 120b.

[0055] Typically, the reduced contrast zone of a lens comprises hundreds or thousands of dots, and the size of these dots can be the same or can vary across each lens. For example, the size can increase or decrease as a function of the dot's position, such as as measured from the clear aperture, and / or as a function of its distance from the lens edge. In some examples, the size of the dots changes monotonically with increasing distance from the lens center (e.g., monotonically increasing or monotonically decreasing). In some cases, the monotonically increasing / decreasing size includes a linear change in the diameter of the protrusion as a function of distance from the lens center.

[0056] Figure 1CThe dots shown are irregularly arranged on the lens surface. Typically, the dots are arranged such that they collectively provide sufficient contrast reduction at the observer's periphery for myopia reduction. Typically, smaller dot spacing results in greater contrast reduction. The dots can usually be spaced apart or overlap each other. For spaced-apart dots, the distance between adjacent dots can be from 0.05 mm (e.g., about 0.1 mm or greater, about 0.15 mm or greater, about 0.2 mm or greater, about 0.25 mm or greater, about 0.3 mm or greater, about 0.35 mm or greater, about 0.4 mm or greater, about 0.45 mm or greater, about 0.5 mm or greater, about 0.55 mm or greater, about 0.6 mm or greater, about 0.65 mm or greater, about 0.7 mm or greater, about 0.75 mm or greater) 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).

[0057] Typically, the coverage of the lens by the dots can be varied as desired. Here, coverage refers to the proportion of the total area of ​​the lens, as projected onto the xy-plane corresponding to the dots. Typically, a lower dot coverage will produce less scattering than a higher dot coverage (assuming the dots are discrete, i.e., they do not merge to form larger dots). Dot coverage can vary from 10% or more to about 75%. For example, dot coverage can be 15% or more, 20% or more, 25% or more, 30% or more, 35% or more, 40% or more, 45% or more, such as 50% or 55%. Dot coverage can be selected based on the user's level of comfort, for example, to provide a sufficiently comfortable level of peripheral vision so that the wearer will voluntarily wear the glasses for extended periods of time (e.g., all day).

[0058] It is assumed that light incident on the lenses in the reduced contrast regions 130a and 130b between the point objects from the scene contributes to the image of the scene on the user's retina, while light incident on the point objects does not. Furthermore, light incident on the point objects still transmits to the retina, thus the reduced contrast regions 130a and 130b have the effect of reducing image contrast without substantially reducing light intensity at the retina. Accordingly, it is assumed that the amount of contrast reduction in the user's peripheral field of view is related to (e.g., approximately proportionally) the proportion of the surface area of ​​the reduced contrast regions covered by the point objects. Typically, the point objects occupy at least 10% (e.g., 20% or more, 30% or more, 40% or more, 50% or more, such as 90% or less, 80% or less, 70% or less, 60% or less) of the reduced contrast regions 130a and 130b (as measured in the xy plane).

[0059] Typically, dot patterns reduce the contrast of an image of an object in the wearer's peripheral vision without significantly degrading the viewer's visual acuity in that area. Peripheral vision here refers to the field of view outside the field of view of the sharp aperture. Image contrast in these areas can be reduced by 40% or more (e.g., 45% or more, 50% or more, 60% or more, 70% or more, 80% or more) relative to the image contrast seen with the sharp aperture of the determined lens. The contrast reduction can be set according to the needs of each individual case. Typical contrast reduction is considered to be in the range of approximately 50% to 55%. A contrast reduction below 50% may be used for very mild cases, while more sensitive subjects may require a contrast reduction above 55%. As determined by subjective refraction, peripheral visual acuity can be corrected to 20 / 30 or better (e.g., 20 / 25 or better, 20 / 20 or better) while still achieving a meaningful contrast reduction.

[0060] Here, contrast refers to the difference in illuminance between two objects within the same field of view. Correspondingly, a decrease in contrast refers to a change in this difference.

[0061] Contrast and contrast reduction can be measured in various ways. In some embodiments, contrast can be measured based on the brightness difference between different portions of a standard pattern—such as a black-and-white checkerboard of squares—obtained under controlled conditions through the sharp aperture and dot pattern of the lens.

[0062] 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 transmission of a stimulus, where bright and dark areas are sinusoidally modulated at different "spatial frequencies." These stimuli appear as alternating bright and dark bars, with the intervals between the bars varying within a range. For all optical systems, the transmission of contrast is lowest for stimuli with the highest sinusoidal variation in spatial frequency. The relationship describing the transmission of contrast at all spatial frequencies is the OTF. The OTF can be obtained by employing a Fourier transform of the point spread function. The point spread function can be obtained by imaging a point source through the lens onto a detector array and determining how light from a single point is distributed across the detectors.

[0063] In the case of conflict measurement, OTF is the preferred technique.

[0064] In some embodiments, contrast can be estimated based on the ratio of the area of ​​the lens covered by the dots to the area of ​​the clear aperture. In this approximation, it is assumed that all light striking the dots becomes uniformly dispersed across the entire retinal area, which reduces the amount of light available in the brighter areas of the image and adds light to the darker areas. Accordingly, the contrast reduction can be calculated based on light transmission measurements through the clear aperture of the lens and the dot pattern.

[0065] Contrast can also be clinically measured by measuring changes in visual acuity performance in observers wearing lenses (such as the Snellen or ETDRS alphabetic graph) and / or by contrast sensitivity tests (such as the Pelli Robson graph). Contrast changes can be less than one line (i.e., 5 letters), approximately 0.5 lines, one line, two lines, or three lines or greater. This can also be measured in LogMAR units less than or approximately 0.05, 0.10, 0.20, or 0.30 or greater.

[0066] As previously mentioned, the size, spacing, and arrangement of dot patterns can typically vary. In some embodiments, the dot pattern is characterized by, for example, a gradient in the size and / or spacing of the dots. The dot pattern can also be characterized by a gradient in the scattering efficiency of the dots (e.g., due to refractive index mismatch and / or shape gradient of each dot). Graded dot patterns can reduce the conspicuousness of the pattern. For example, a gradient transition from the sharp portion to the scattering portion of the lens can be less noticeable than a sharp transition.

[0067] Lenses 110a and 110b can be formed from stock lenses. Lenses can be made from materials such as polycarbonate or Trivex. The lens is formed from conventional ophthalmic lens materials. The lens may include one or more coatings or other surface treatments, including, for example, hard coatings, photochromic coatings, blue filters, anti-reflective coatings, etc.

[0068] Typically, ophthalmic lenses 110a and 110b can be either clear or tinted. That is, the lenses can optionally be optically transparent to all visible wavelengths, appearing clear and / or colorless, or they can include spectral filters, appearing tinted. For example, ophthalmic lenses may include filters that reduce the amount of red light transmitted to the wearer. It is believed that excessive stimulation of the L-cone in the human eye (especially in children) can lead to suboptimal eye elongation and myopia. Accordingly, using ophthalmic lenses to spectrally filter red light can further reduce myopia in the wearer.

[0069] Typically, the dots 112 can be provided as protrusions and / or depressions on one or both surfaces of each lens, and / or as scattering inclusions in the lens material itself. In some examples, the dots can be formed by an array of protrusions on the surface (e.g., the rear or front surface) of each lens in lenses 110a and 110b.

[0070] The protrusion can be formed from an optically transparent material having a similar refractive index to the lens below—1.60 for polycarbonate (PC). For example, in embodiments where the lens is formed of polycarbonate, the protrusion can be formed from a polymer having a similar refractive index to PC, such as photoactivated polyurethane or epoxy-based plastics. Besides PC, the lens itself can also be made from allyl diethylene glycol carbonate plastics, polyurethane-based monomers, or other impact-resistant monomers. Alternatively, the lens can be made from one of the denser, high-refractive-index plastics with a refractive index greater than 1.60. In some embodiments, the lens is made from an optically transparent material with a lower refractive index (e.g., CR39 has a refractive index of 1.50, and Trivex has a refractive index of 1.53).

[0071] Each dot 112 is sized and shaped to scatter light incident on it. Typically, the dot scatters a portion of the incident light forward and a portion backward. The forward-scattered light typically exits the lens from the side opposite to where it was incident, while the backward-scattered light is scattered away from the lens from the side from which it was incident. Figure 2 The diagram illustrates this light scattering, showing that lens 110a has a scattering center, such as a dot 112, on its front surface. Lens axis 203 is shown for reference, for example, corresponding to the axis of rotational symmetry of a lens in which the lens corrects only for spherical aberration.

[0072] Four incident rays 206, 208, 210, and 212, each incident on a different point 112, are shown. Depending on the angle of incidence and the shape of the point, the light can be forward-scattered (rays 214 and 218) and / or backward-scattered (rays 216 and 220). Depending on the forward scattering angle and the wearer's visual axis, the forward-scattered light entering the eye 224 can be incident on or away from the wearer's fovea, or can be completely directed away from the retina. Typically, unlike other light focused by the lens, the scattered light will not image on the wearer's retina. Scattered light incident on the wearer's fovea does not necessarily reduce the contrast of the wearer's foveal vision, which can be undesirable. Scattered light incident on the retina away from the fovea can reduce the contrast of the wearer's peripheral field of vision, thereby reducing myopia progression, as previously discussed. This forward-scattered light can be considered a "therapeutic light." In some (but not all) cases, other forward-scattered light, such as light incident outside the fovea or peripheral field of vision, is not considered therapeutic. Accordingly, it is desirable to expect forward scattering of light in directions that contribute to reducing peripheral visual contrast but not to reducing foveal contrast. Alternatively, in some cases, forward-scattered light that contributes to reducing foveal contrast can be acceptable.

[0073] Typically, light scattered into a cone that contributes to reduced contrast in the peripheral field of view is considered narrow-angle forward scattered light, while light outside the cone is considered wide-angle forward scattered light. Figure 2 The solid angle depicted by the outline 222 of the cone with a cone angle 223 can be used to distinguish between narrow-angle scattering and wide-angle scattering. Light scattered inside the cone, such as ray 218, is narrow-angle forward scattered light, while light scattered outside the cone, such as ray 214, is wide-angle scattered light. For narrow-angle scattering, the cone angle can be in the range of 1 degree to 5 degrees. In some examples, the cone angle for narrow-angle scattering can be 2.5 degrees.

[0074] Some of the incident rays are backscattered; for example, incident rays 208 and 212 are backscattered, becoming backscattered rays 216 and 220. This backscattered light can be seen by people other than the wearer, making the dot object conspicuous to those looking at the wearer. Accordingly, it is desirable to reduce (e.g., by increasing (e.g., maximizing) the amount of forward-scattered light to a narrow angle while minimizing the amount of backscattered light, until a threshold amount sufficient to achieve the aforementioned therapeutic effect of reducing peripheral image contrast.

[0075] For light incident on a region of reduced contrast, the amount of forward-scattered and / or back-scattered light can be measured using a scanning scatterometer. A scanning scatterometer is an instrument having a light source such as a laser and a detector such as a single-pixel detector. The sample is illuminated by a collimated beam from the light source, and the detector is scanned on a sphere surrounding the sample to generate a map of the locations where the light has passed. Using this method, the total amount of back-scattered light incident on a region of reduced contrast can be 12% or less, 10% or less, 9% or less, 8% or less, 7% or less, 6% or less, 5% or less, 4% or less, 3% or less, 2% or less, or 1% or less. The percentage of back-scattered light can be 50% or less, 40% or less, 30% or less, 20% or less, 10% or less, or less than 10%, such as 9% or less, 8% or less, 7% or less, 6% or less, 5% or less, 4% or less, 3% or less, 2% or less, or 1%. The percentage of forward-scattered light can be 50% or greater, 60% or greater, 70% or greater, 80% or greater, 90% or greater, 91% or greater, 92% or greater, 93% or greater, 94% or greater, 95% or greater, 96% or greater, 97% or greater, 98% or greater, such as 99%. The percentage of forward-scattered light scattered into the narrow-angle scattering direction (discussed above) can be 50% or greater, 60% or greater, 70% or greater, 80% or greater, 90% or greater, such as 95%.

[0076] In some cases, the amount of forward-scattered and / or back-scattered light can be determined by optical computer simulation using commercially available optical design software such as Zemax (from AnSys) or Code V (from Synopsys). Using this method, the total amount of back-scattered light incident on the reduced contrast region can be 12% or less, 10% or less, 9% or less, 8% or less, 7% or less, 6% or less, 5% or less, 4% or less, 3% or less, 2% or less, or 1% or less. The percentage of back-scattered light can be 50% or less, 40% or less, 30% or less, 20% or less, 10% or less, or less than 10%, such as 9% or less, 8% or less, 7% or less, 6% or less, 5% or less, 4% or less, 3% or less, 2% or less, or 1%. The percentage of forward-scattered light can be 50% or more, 60% or more, 70% or more, 80% or more, 90% or more, 91% or more, 92% or more, 93% or more, 94% or more, 95% or more, 96% or more, 97% or more, 98% or more, such as 99%.

[0077] Therefore, the dot pattern in regions 130a and 130b with reduced contrast, as well as the shape of each dot, are typically selected based on various design parameters to provide the desired level of light scattering, thereby providing optimal therapeutic effect while minimizing the amount of backscattered light. These design parameters typically include, for example, the dot pattern (i.e., dot density, dot density distribution, relative position of the dots, etc.), their size and shape, their refractive index, and other properties such as the transmission and reflection properties of the dots across various wavelengths. Ideally, the dot pattern is selected to provide high visual acuity at the fovea and reduced image contrast in other parts of the retina, with sufficiently low discomfort to allow for prolonged continuous wear. For example, it is possible to expect children to wear the glasses comfortably for most, if not all, of the day. The dot size, shape, and dot pattern can also be selected to provide a relatively small amount of backscattered light.

[0078] Examples of dot patterns are described in US20190033619A1 entitled “Ophthalmic lenses for treating myopia” and US20190235279A1 entitled “Ophthalmic lenses with light scattering for treating myopia”, the entire contents of which are incorporated herein by reference. Further examples of dot patterns are described below.

[0079] Various metrics can be used to evaluate the performance of dot patterns in order to optimize them for use in myopia reduction eyeglasses. For example, dot patterns can be empirically optimized, for instance, based on physical measurements of lenses with different dot patterns. Light scattering, for example, can be characterized based on haze measurements, such as international testing standards like degrees (e.g., ASTM D1003 and BS EN ISO 13468). Conventional haze meters, such as BYK-Gardner haze meters (e.g., the Haze-Gard Plus instrument), can be used to measure how much light is completely transmitted through the lens, the amount of light transmitted undisturbed (e.g., within 0.5 degrees), how much deflection is greater than 2.5 degrees, and clarity (amount within 2.5 degrees). Other equipment can also be used to characterize light scattering for the purpose of empirically optimizing scattering patterns. For example, equipment that measures light diffusion by measuring light in a ring of approximately 2.5 degrees (e.g., equipment from Hornell) can be used.

[0080] Alternatively or additionally, dot patterns can be optimized using computer modeling software (e.g., Zemax or Code V).

[0081] Alternatively or additionally, point patterns can be empirically optimized by designing various patterns and measuring forward and backward scattering using the methods described above.

[0082] In some examples, it is possible to design dot shapes and patterns based on the optimization of a dot spread function, which is a representation of the image of scattering centers on the retina. For example, the size, shape, and spacing of the scattering centers can be varied to evenly diffuse the illumination of the retina, so that the retina outside the fovea is uniformly covered by scattered light, thereby reducing (e.g., minimizing) the contrast of the retina in that area.

[0083] Alternatively or additionally, dot shapes and patterns can be designed based on optimization of the modulation transfer function, which refers to the spatial frequency response of the human visual system. For example, the size, shape, and spacing of the scattering centers can be varied to smooth the attenuation across a range of spatial frequencies. The design parameters of the dot pattern can be altered to increase or decrease certain spatial frequencies as desired. Typically, the spatial frequencies of interest for vision are 18 cycles per degree on the fine side and 1.5 cycles per degree on the coarse side. The dot pattern can be designed to provide increased signal at certain subsets of spatial frequencies within this range.

[0084] As described above, dots can be provided on one or both surfaces of the lens or within the lens itself. For dots formed on the lens surface, the dots can be formed as protrusions from the lens surface or depressions within the surface. Examples of depressions and protrusions are respectively... Figure 3A and 3B As shown in [the image]. Figure 3A In this design, a dot 301 is formed as a recess in the lens surface 310. In the cross-sectional profile, the shape of the dot 301 is characterized by its width or lateral dimension W and depth D. The width refers to the lateral dimension from one edge of the dot (i.e., where the dot meets the lens surface) to the opposite edge. The depth refers to the vertical dimension of the dot, measured from its edge to its base. Here, the recess has a parabolic profile that is vertically axially symmetric about its center, the vertical axis of which corresponds to the surface normal of the lens surface 310 at the center of the dot. The profile of the dot can be the same in other cross-sections (e.g., for a dot with a circular perimeter shape) or can vary for different cross-sections. Examples of dot perimeter shapes are discussed below.

[0085] Typically, width, depth, and shape can be varied as desired. As discussed further below, width and depth can affect how a point scatters light. In some examples, the width of a point (e.g., a maximum width that varies depending on the cross-section) ranges from 10 μm to 2,000 μm (e.g., 50 μm or greater, 100 μm or greater, 150 μm or greater, 200 μm or greater, 250 μm or greater, 300 μm or greater, 350 μm or greater, 400 μm or greater, 450 μm or greater, 500 μm or greater, 600 μm or greater, 700 μm or greater). 0 μm or larger, 800 μm or larger, 900 μm or larger, and such as 1,750 μm or smaller, 1,500 μm or smaller, 1,250 μm or smaller, 1,000 μm or smaller, 900 μm or smaller, 800 μm or smaller, 700 μm or smaller, 600 μm or smaller, 500 μm or smaller, such as in the range from 100 μm to 400 μm, in the range from 200 μm to 350 μm). The dot-like particles 301 can have depths ranging from 2 μm to 500 μm (e.g., 5 μm or greater, 10 μm or greater, 20 μm or greater, 30 μm or greater, 40 μm or greater, 50 μm or greater, 60 μm or greater, 70 μm or greater, 80 μm or greater, 90 μm or greater, 100 μm or greater, 110 μm or greater, 120 μm or greater, 130 μm or greater, 140 μm or greater, 150 μm or greater, 175 μm or greater). 200 μm or larger, and such as 450 μm or smaller, 400 μm or smaller, 350 μm or smaller, 300 μm or smaller, 250 μm or smaller, 200 μm or smaller, 150 μm or smaller, 120 μm or smaller, 100 μm or smaller, 50 μm or smaller, 30 μm or smaller, 20 μm or smaller, such as in the range from 10 μm to 150 μm, such as in the range from 20 μm to 100 μm, such as in the range from 30 μm to 80 μm).

[0086] The depth of the recess can be less than the width. For example, the ratio D / W can be in the range of 1 / 50 to 9 / 10 (e.g., 1 / 40 or greater, 1 / 30 or greater, 1 / 20 or greater, 1 / 10 or greater, 1 / 5 or greater, 1 / 4 or greater, 1 / 3 or greater, 1 / 2 or greater, and such as 4 / 5 or less, 7 / 10 or less, 3 / 5 or less, 1 / 2 or less, 1 / 3 or less, 1 / 4 or less).

[0087] In some examples, the depth is 20 μm or less, and the width (e.g., the maximum width) is 100 μm or more.

[0088] Points with a depth less than their width—for example, the D / W ratio described above—are thought to have reduced backscattering compared to point objects with a similar or greater depth than their width. Reduced backscattering is generally associated with shallower point objects (e.g., those with a depth of 50 μm or less). Without being bound by theory, reduced backscattering could be due to fewer ray paths, including more likely multiple reflections as the depth or aspect ratio of the point object increases.

[0089] Figure 3B A point-like feature is shown formed as a protrusion 302 having a width W and a height (e.g., maximum height) H. The width range of the protrusion 302 can be the same as that of the recess of the point-like feature 301. For the recess of the point-like feature 301, the height range can be the same as the depth range D. Similar to the recess of the point-like feature 301, the higher the aspect ratio H / W of the protrusion 302, the higher the backscattering rate, which is opposite to forward scattering.

[0090] Although the outlines of dot 132 and dot 134 are respectively in Figure 3A and 3B The cross-section depicted is parabolic, but the point can have other contour shapes. For example, in some cases, the point is pit-shaped with a central depression extending to a depth below the lens surface, surrounded by an edge 316 extending to a height above the lens surface. Figure 3C An example of a pit-shaped dot 303 is shown. The dot 303 has a width W and a depth D as defined above. Additionally, the recess 313 has a width WD smaller than the width W of the entire dot 303. The edge 316 has a height (e.g., a maximum height varying around the perimeter) HR and a width (e.g., a maximum width varying around the perimeter) WR. W and D can be within the ranges described above. WD can be 1,500 μm or less (e.g., 1,000 μm or less, 800 μm or less, 700 μm or less, 600 μm or less, 500 μm or less, 400 μm or less, 300 μm or less, 250 μm or less, 200 μm or less, 150 μm or less, and such as 50 μm or more, 75 μm or more, 100 μm or more, 120 μm or more, 150 μm or more, 200 μm or more).

[0091] HR can be smaller than D. For example, HR can be D / 2 or smaller (e.g., D / 3 or smaller, D / 4 or smaller, D / 5 or smaller, D / 6 or smaller, D / 8 or smaller, D / 10 or smaller). In some cases, HR is 20 μm or smaller (e.g., 15 μm or smaller, 12 μm or smaller, 10 μm or smaller, 8 μm or smaller, 5 μm or smaller, 3 μm or smaller, 2 μm or smaller).

[0092] WR can be 20 μm or smaller (e.g., 15 μm or smaller, 12 μm or smaller, 10 μm or smaller, 8 μm or smaller, 5 μm or smaller, 3 μm or smaller, 2 μm or smaller).

[0093] Dot-like objects can have irregular surfaces. Figure 3D An example of a dot-like feature in the form of a recess 304 with an irregular surface is shown. Here, the recess 304 has a depth D and a width W as defined above. The edge 317 has a height HR and a width as described above. In addition, the central recess 314 is characterized by sidewalls 318a and 318b and a floor 319. The floor 319 extends over a width WF and is characterized by an irregular surface with a height variation dF. Here, WF is measured from the base of one sidewall 318a to the base of the opposite sidewall 318b. The base of the sidewall can be identified as the location of a local minimum in the cross-sectional surface profile of the recess where the height of the floor begins to increase.

[0094] Where the sidewalls are vertical, WD = WF. Typically, WD will be the same as or greater than WF. For example, WF can be 0.95WD or less (e.g., 0.9WD or less, 0.8WD or less, 0.75WD or less, 0.7WD or less, 0.65WD or less, 0.6WD or less, 0.55WD or less, 0.5WD or less, 0.45WD or less, 0.4WD or less). In some examples, WF is 500 μm or less (e.g., 400 μm or less, 300 μm or less, 250 μm or less, 200 μm or less, 150 μm or less, 100 μm or less, 80 μm or less, such as about 20 μm or more, 50 μm or more, 75 μm or more, 100 μm or more).

[0095] In some cases, small values ​​of dF correspond to a smooth and flat bottom of 319. In the examples, dF can be 0.5D or smaller (e.g., 0.4D or smaller, 0.3D or smaller, 0.2D or smaller, 0.15D or smaller, 0.1D or smaller, 0.075D or smaller, 0.05D or smaller). dF can be 50μm or smaller (e.g., 40μm or smaller, 30μm or smaller, 20μm or smaller, 10μm or smaller, 5μm or smaller, 3μm or smaller, 2μm or smaller, such as 1μm or larger, 2μm or larger, 3μm or larger, 5μm or larger, 8μm or larger, 10μm or larger).

[0096] In some examples, WF is 0.5W or greater, and dF is 0.2D or less.

[0097] Without being bound by theory, it is considered that a dot with relatively steep sidewalls (e.g., where WD is not much larger than WF), relatively shallow (e.g., D is 50 mm or less), and relatively flat bottom (e.g., dF is 0.2D or less) can have relatively little backscattered light and can preferably scatter light forward to a relatively narrow angle. Accordingly, such a dot can provide a lens with reduced conspicuousness and high therapeutic efficacy.

[0098] Typically, conventional surface measurement techniques such as SEM microscopy and optical interferometry, as well as conventional image analysis techniques for extracting dimensions from images acquired using measurement techniques, can be used to determine the shape of point-like structures formed on the surface of a lens, such as those described above.

[0099] As previously mentioned, in addition to the cross-sectional profile, the shape of surface dots is also defined by the shape of their periphery. Typically, dots can be formed with any peripheral shape having resolution subject to the methods used to form them. Generally, when forming dots using methods involving depositing, removing, or modifying material on the surface of a lens, dots can be formed by scanning a dot-forming apparatus, such as a laser (an example discussed below), along a path to alter the lens surface at that location and delineate the shape of the dots on the lens surface. Figures 4A to 4S The diagram illustrates various path shapes used to form the periphery of different dots. Depending on the resolution of the dot-forming apparatus and the size of the dots (e.g., the width as previously discussed), it is possible to scan the dot-forming apparatus along multiple paths (one within another) to modify the entire lens surface of the dots.

[0100] exist Figure 4A In the first example, the dot 401 has a pentagonal star-shaped periphery. The dot is formed by scanning the device concentrically along a first star-shaped path 401a and a second star-shaped path 401b, inside path 401a and concentrically with path 401b. Each path in paths 401a and 401b can correspond to about Figure 3D The edge of the description.

[0101] Figure 4B A pear-shaped dot 402 is shown formed by tracing the dot-forming device along a first path 402a and a second path 402b within the first path 402a. The shapes of the first path 402a and the second path 402b can be substantially the same, wherein the second path 402b is reduced in size. Each path in paths 402a and 402b includes areas with sharp turns and smooth turns.

[0102] Figure 4CA point 403 is shown, which is generally trapezoidal in shape and formed by a single path 403a. The path 403a includes a relatively small segment on its upper side compared to the rest of the segments that form the trapezoidal shape.

[0103] Figure 4D The diagram illustrates a path of dots 404 formed by the lens forming apparatus traveling along two elliptical paths 404a and two straight lines 404b. Path 404a is smooth and curved, and line 404b is linear.

[0104] Figure 4E An example of an octagonal dot 405 formed by scanning the dot-forming apparatus along a continuously segmented spiral path 405a is shown. Since the beam following the path 405a has a finite width, the resulting dot 405 can be a depression with an irregular depth within another part of the path 405a.

[0105] Figure 4F Another example of a polygonal dot formed by scanning the dot-forming apparatus along a continuously segmented spiral path 406a is shown. Compared to path 405a, path 406a has fewer linear segments, and the outline of dot 406 will be different from the outline of dot 405.

[0106] Figure 4G An example of an approximately circular dot 407 formed by scanning the dot-forming apparatus along a continuous spiral path 407a is shown. Path 407a is smoother than paths 405a and 406a.

[0107] Figure 4H A dumbbell-shaped dot 408 is shown formed by the dot-forming device traveling along a first path 408a and a second path 408b within the first path 408a. Although both paths 408a and 408b are dumbbell-shaped, the two paths can have different parameters, such as aspect ratio.

[0108] Figure 4I A trapezoidal dot 409 is shown formed by the dot-forming device traveling along a first path 409a and a second path 409b within the first path 409a. Each path in paths 409a and 409b is similar to path 403a.

[0109] Figure 4J A crescent-shaped dot 410 is shown formed by the dot-forming device traveling along a first path 410a and a second path 410b within the first path 410a. Since the path 410a is relatively narrow, for example, having a high aspect ratio, the path 410b can be much shorter than the path 410a while still maintaining a relatively uniform bottom.

[0110] Figure 4K A zigzag dot 411 is shown formed by a dot-forming device traveling along a single closed path 411a. The path 411a typically includes linear segments that intersect at various angles.

[0111] Figure 4L A cat-head shaped dot 412 is shown formed by the dot-forming apparatus traveling along a first path 412a and a second path 412b within the first path 412a. By following the path 412b within the path 412a with a beam, for example, the overall depth profile within the dot 412 can be more consistent compared to following only the path 412a.

[0112] Figure 4M Another crescent-shaped dot 413 is shown, formed by the dot-forming device traveling along a first path 413a and a second path 413b within the first path 413a. Compared to the crescent-shaped dot 410, the dot 413 has a lower aspect ratio, and therefore the first path 413a and the second path 413b are closer in size to paths 410a and 410b.

[0113] Figure 4N A cone-shaped dot 414 is shown formed by the dot-forming device traveling along a first path 414a and a second path 414b within the first path 414a. Both paths 414a and 414b consist of slightly curved sections.

[0114] Figure 4O A polygonal dot 415 is shown formed by a dot-forming device traveling along a series of hexagonal paths 415a, such as a cellular grid. The beam can follow various routes to form paths 415a.

[0115] Figure 4P A circular dot 416 is shown formed by the dot-forming device traveling along a first path 416a and a second path 416b within the first path 416a. Both paths 416a and 416b are circular and concentric.

[0116] Figure 4Q An elliptical dot 417 is shown formed by the dot-forming device traveling along a first path 417a and a second path 417b within the first path 417a. Both paths are elliptical and concentric.

[0117] Figure 4R A rectangular dot 418 is shown formed by the dot-forming device traveling along a first path 418a and a second path 418b within the first path 418a. Both paths are rectangular and concentric.

[0118] Figure 4SA square dot 419 is shown formed by the dot-forming apparatus traveling along a first path 419a, a second path 419b within the first path 419a, and a third path 419c within the second path 419b. Each path is square. Because the widths of paths 419a and 419b are relatively large compared to the width of the beam following those paths, an additional path 419c is provided to ensure a relatively smooth bottom.

[0119] Typically, any number of closed paths can be scanned sequentially to form a dot with a desired shape, size, and base. Other shapes are also possible. Shapes that can be formed by scanning the dot-forming device along a single continuous path may be advantageous because they can be formed more efficiently (e.g., faster) than shapes formed by multiple separate paths. This is because a single continuous path typically avoids the need to reset the dot-forming device by moving it from one path to another.

[0120] The effects of point size and shape on scattering can be empirically studied through physical light scattering experiments and / or optical computer simulations. Optical simulation software is used to model the forward and backward scattering properties of scatterers with simple geometries. For simulation purposes, spectacle lenses with plano lens dimensions (124mm front R, 123.2mm rear R, 2mm thickness) and model eyes of the same size as the human eye are modeled. Three fields of 0 degrees, 20 degrees, and 40 degrees (full field) are used in the model to illustrate central, near-peripheral, and intermediate / far-peripheral vision. In each case, all point objects are modeled on the rear surface of the lens (i.e., the surface facing the wearer).

[0121] The results of these simulations are Figure 5A and 5B As shown in the drawing. Here, Figure 5A The number of simulated light rays striking the wearer's retina with five different point objects is shown. Figure 5B The diagram shows the number of simulated rays backscattered for the same five different point objects. In each plot, the x-axis represents the height or depth of the point object, depending on whether the point object is convex or concave.

[0122] Lines 501a and 501b correspond to point-like structures formed by hemispherical protrusions. Increasing the height of these protrusions does not significantly change the total number of rays striking the retina, but it alters the distribution of forward and backward scattering.

[0123] Lines 502a and 502b correspond to hemispherical depressions. Ray tracing shows that the hemisphere with the minimum depth (10 μm) provides the maximum forward scattering and the minimum backscattering to the retina. Increasing the depth of the hemisphere reduces the amount of light impacting the retina and increases backscattering. The analysis shows that the trend is not linear; that is, at a depth of ~50 μm, forward scattering does not decrease further, and at a depth of ~70 μm, backscattering does not increase further.

[0124] Lines 503a and 503b correspond to concave areas shaped like hemispheres with concave ends. Ray tracing shows that the concave hemisphere with the minimum depth (10 μm) provides the maximum forward scattering and the minimum backscattering to the retina. Increasing the depth of the hemisphere reduces the amount of light impacting the retina and increases backscattering. The sharpest increase in backscattering occurs between depths of 40 μm and 60 μm, and the sharpest decrease in forward scattering occurs between depths of 10 μm and 30 μm. This analysis shows that at a depth of ~50 μm, forward scattering does not decrease significantly further, and at a depth of ~60 μm, backscattering does not increase further.

[0125] Lines 504a and 504b correspond to concave shapes that are elongated hemispheres in the axial direction of the lens. Ray tracing shows that the hemisphere with the minimum Z-height (50 μm) provides the maximum forward scattering and the minimum backscattering to the retina. Increasing the length of the hemisphere in the Z-direction reduces the amount of light hitting the retina and increases backscattering; however, the rate of change is significantly smaller than that found by adjusting the depth of the hemisphere.

[0126] Lines 505a and 505b correspond to concave shapes of elongated hemispheres with concave ends. Ray tracing shows that the elongated concave hemisphere with the minimum height (50 μm) provides the maximum forward scattering and the minimum backscattering to the retina. Increasing the length of the concave hemisphere reduces the amount of light impacting the retina. Increasing the length of the concave hemisphere from 50 μm to 170 μm does not significantly change backscattering; however, there is a sharp increase in backscattering from a height of 170 μm to 240 μm.

[0127] Based on simulations, both the "hemispherical" and "concave hemisphere" exhibited the same trend: increasing depth reduced forward-scattered light and increased back-scattered light. In both the "hemispherical" and "concave hemisphere," the elongation of the scatterer in the Z-direction did not significantly affect either forward or backscattering. However, for the convex, while a reasonable number of rays struck the retina across all depths, backscattering was also high. For larger convex, ray tracing showed minimal impact on vision due to minimal forward scattering. A balance between light scattering and contrast sensitivity of the convex was achieved in the 20 μm to 30 μm range.

[0128] In some examples, the dot object can be designed to deliver reduced narrow-angle scattering and increased wide-angle scattering to produce a uniform light distribution on the retina / low-contrast signal while maintaining acuity through the geometry of the scattering center. For example, the dot object can be designed to generate significantly wide forward scattering (e.g., more than 10%, 20% or greater, 30% or greater, 40% or greater, 50% or greater, with a deflection of more than 2.5 degrees). Narrow-angle forward scattering, i.e., within 2.5 degrees, can remain relatively low (e.g., 50% or less, 40% or less, 30% or less, 20% or less).

[0129] As described above, dots can be formed on or in a lens (e.g., a stock lens) by adding material to the lens, removing material from the lens, and / or by changing the optical properties of the lens material.

[0130] In some examples, dots are formed on the lens surface or within the lens's bulk material by exposing the lens to laser radiation. The laser radiation interacts locally with the lens material (e.g., the bulk material and / or coating material) to produce dots. Typically, lasers can be used to form dots on the surface of a lens or within its bulk material. For example, exposing a lens surface to a laser beam of sufficient energy can produce dots by leaving small indentations and / or roughening patches on the surface. By selectively exposing areas of the lens surface to laser radiation, dot patterns can be formed on the surface. For example, when the laser beam is pulsed, the laser beam can move relative to the surface. Relative movement between the beam and the lens surface can be caused by moving the beam while keeping the surface fixed, moving the surface while keeping the beam fixed, or moving both the beam and the surface.

[0131] Typically, the optical properties of dots formed on a lens surface using a laser can be affected in several ways. For example, the energy density of the laser beam pulse will generally affect the physical and / or chemical interaction between the laser and the lens material. For instance, at certain pulse energies, the lens material can melt at its exposed location to form dots. At some pulse energies, dots can be formed by foaming the lens material. This can occur at higher energies than the melting of the lens. At some pulse energies, the interaction between the laser and the lens material can cause a color change in the lens material (e.g., by carbonization). Still in other instances, lens material can be removed from the lens surface by ablation.

[0132] Other laser parameters can also affect the properties of the dots formed using a laser. These include the laser wavelength, irradiation time (e.g., how long each dot location is irradiated), and number of passes (e.g., irradiating one area multiple times, with other areas irradiated between each pass), each of which can be selected to achieve the desired surface modification. Additionally, the interaction between the laser and the lens material will depend on the lens material itself. For example, dots in a lens material with a relatively high glass transition temperature can be formed using lower pulse energy or fewer pulses compared to dots in a lens material with a relatively high glass transition temperature.

[0133] The resolution of the laser beam at the lens surface can be smaller than the desired dot size. For example, the beam resolution (determined, for instance, from the FWHM of the intensity profile) can be about 50% or less of the dot size (e.g., about 25% or less, about 10% or less, about 5% or less, about 1% or less). In some embodiments, the beam can form features with a size of 100 μm or less (e.g., 50 μm or less, 20 μm or less, 10 μm or less, 5 μm or less). In such cases, the laser can be used to form dots with complex peripheral shapes and / or a maximum width significantly larger than the focused dot size, but doing so involves scanning the laser along the path to form the dot.

[0134] refer to Figure 6 A laser system 600 for forming dots on the surface of a lens includes a laser 620, a beam chopper 630, focusing optics 640, a mirror 650, and a platform 670. The laser 620 directs a laser beam toward the mirror 650, which deflects the beam toward a lens 601, which is positioned relative to the mirror 650 via the platform 670. An actuator 660 (e.g., a piezoelectric actuator) is attached to the mirror 650. The platform includes a lens mounting surface 680 that supports the lens 601. The laser system 600 also includes a controller (e.g., a computer controller) in communication with the laser 620, the beam chopper 630, and the actuator 660.

[0135] A beam chopper 630 and a focusing optics 640 are located in the beam path. The chopper 630 periodically blocks the beam, exposing the lens 601 to discrete laser pulses. The focusing optics 640, typically including one or more optical power elements (e.g., one or more lenses), focuses the beam onto a sufficiently small spot on the surface of the lens 601, such that the area ablated by the beam on the lens surface corresponds to the desired dot size. An actuator 660 alters the orientation of the reflector 650 relative to the beam to scan the pulsed beam onto different target points on the lens surface. A controller 610 coordinates the operation of the laser 620, the chopper 630, and the actuator 660, causing the laser system to form a predetermined dot pattern on the lens.

[0136] In some embodiments, platform 670 also includes an actuator. The platform actuator can be a multi-axis actuator, for example, moving the lens in two lateral dimensions orthogonal to the beam propagation direction. Alternatively or additionally, the actuator can move the platform along the beam direction. Moving the platform along the beam direction can be used to maintain an exposed portion of the lens surface at the focal point of the beam, regardless of the curvature of the lens surface, thereby maintaining a substantially constant point size across the lens surface. The platform actuator can also be controlled by a controller 610, which coordinates the platform movement with other components of the system. In some embodiments, a platform actuator is used instead of a mirror actuator.

[0137] Typically, laser 620 can be any type of laser capable of generating light with sufficient energy to modify lens materials (e.g., the host lens material or coating) to form dot-like patterns. The laser can have wavelengths in the UV, visible, or IR portions of the electromagnetic spectrum. Gas lasers, chemical lasers, dye lasers, solid-state lasers, and semiconductor lasers can be used. In some embodiments, infrared lasers, such as CO2 lasers (having emission wavelengths of 9.4 μm or 10.6 μm), can be used. Commercially available laser systems can be used, such as CO2 laser systems (e.g., a 60W VLS 4.60 system) manufactured by Universal Laser Systems, Inc. (Scottsdale, AZ). In some embodiments, femtosecond lasers can be used. For example, commercial femtosecond laser systems, such as those manufactured by Trumpf (Santa Clara, CA) (e.g., the TruMicro 2030 laser device as the TruLaserStation 5005), can be used to form dot-like patterns of desired shapes and sizes. Such laser devices can achieve burst energies much higher than the maximum energy of a single pulse in their burst mode, resulting in higher ablation rates. This exemplary laser system is capable of providing pulse durations of less than 400 femtoseconds with a maximum pulse energy of 50 μJ.

[0138] Typically, the pulse duration and pulse energy are selected to provide dots of a desired size. For example, in some embodiments, the laser 620 forms a predetermined dot pattern on the lens 601 by melting material at the surface of the lens 601. For example, when laser etching causes the molten material of the lens 601 to expand, the laser 620 heats and melts a portion of the surface of the lens 601 to form a predetermined pattern, resulting in raised marks forming the predetermined dot pattern.

[0139] In some embodiments, the laser 620 uses laser foaming to form a predetermined dot pattern on the lens 601. For example, the laser 620 uses laser foaming to melt and fix a polymer material onto the lens 601, wherein the laser 620 marks the foam, thus forming the predetermined dot pattern.

[0140] In some examples, laser 620 uses laser marking to form a predetermined dot pattern on lens 601. For example, laser marking forms the predetermined dot pattern on lens 601 by causing a color change, for example, due to a chemical or physical change in the portion of lens 601 where the predetermined dot pattern is formed. In another example, laser 620 forms the predetermined dot pattern on lens 601 by charring lens 601, thereby forming the predetermined dot pattern on lens 601.

[0141] In some embodiments, laser 620 uses ablation to form a predetermined dot pattern on lens 601. For example, laser 620 is used to ablate (e.g., remove material) lens 601 by evaporating or sublimating lens 601 to form the predetermined dot pattern. After ablation, pits may be formed on lens 601.

[0142] In some examples, to reduce the conspicuousness of the dot pattern (e.g., to reduce backscattering and reflection at the scattering center due to ablation pits), the surface of the ablation pits on lens 601 is modified to reduce surface roughness (e.g., to produce dots with a large bottom size relative to the dot size and a small dF relative to the depth of the dot). Reducing surface roughness can reduce the effects of small-angle light scattering (e.g., where the scattering angle is less than 3 degrees). For example, the surface of the ablation pits on lens 601 can be modified by a second pass ablation to melt the rough surface of the ablation pits (e.g., by using lower energy ablation). Lower energy ablation can be performed, for example, by defocusing laser 620 (e.g., by increasing the beam width of laser 620). In some embodiments, further reducing the conspicuousness of the dot pattern involves defocusing laser 620 over multiple iterations. For example, defocusing the laser 620 occurs in several passes (e.g., each second, third, fourth, etc. ablation) with increasing defocus (e.g., as the beam width increases each time) to affect the taper of the pit (e.g., to feather or smooth the pit edges). In some specific embodiments, reducing the prominence of the dot pattern involves performing multiple overlapping ablations to combine a single ablation pit with multiple overlapping ablation pits.

[0143] In some embodiments, reducing the conspicuousness of the dot pattern involves coating an anti-reflective layer on the rear surface of lens 601. In some embodiments, the reflective layer is coated on the front surface of the lens. This is particularly advantageous if laser ablation is performed on the rear surface of lens 601. Typically, laser 620 has a stronger effect on the coating than the lens 601 material, thus affecting the taper of the pits (e.g., feathering or smoothing of the pit edges).

[0144] Figure 7 and Figure 8 Two examples of laser paths used to form dot-like objects, each with a width of 140 μm, are shown. Figure 7 The dot-like shape formed by scanning two discrete paths 710 and 720 is shown. The outer path 710 is octagonal. The inner path 720, with a width of 75 μm, is hexagonal. Scanning these paths involves moving the laser from the first path to the second path without exposing the lens surface.

[0145] Figure 8 The segmented helical path 810 of the laser is shown, which forms in the outer portion 810a of the helical path 810 with... Figure 7The dot matrix shown has the same octagonal shape. The inner portion 810b of the spiral path 810 follows a hexagonal shape rotated 60 degrees relative to the path 720, and the middle portion 810c of the path connects the inner portion 810b and the outer portion 810a. Here, the dot matrix is ​​formed by traveling the laser along a single continuous path, so it is not necessary to move the laser from one path to the next to complete the formation of the dot matrix. Such a dot matrix can be formed faster than a dot matrix involving more than one discrete path. Furthermore, such a path can result in a dot matrix with a smoother bottom compared to a dot matrix of similar size that has been formed by scanning multiple discrete paths.

[0146] This is Figure 9A and 9B as well as Figure 10A and 10B The comparison of the dots shown is obvious; these dots correspond to the use of Figure 8 and Figure 7 The path shown forms point-like structures. Specifically, Figure 9A and 9B The use of, as shown Figure 8 The diagram shows two point-like objects formed by the spiral path. This view of the point-like objects was acquired using optical interferometry. Figure 9B The diagram shows the cross-sectional profile of a section passing through one of the point objects, for example, the height along... Figure 9A The relationship between the positions of line 901 in the diagram. For example, Figure 9A and 9B The dots in the image have a maximum height of 1.262 μm above the surface, for example, 0 μm, and a minimum height of -12.583 μm below the surface, for example, spanning a range of about 14 micrometers.

[0147] Figure 10A It shows the use of Figure 7 The top view shows the three point-like objects formed by the two paths. Figure 10B The diagram shows the outline of one of the points, for example, its height and along... Figure 10A The diagram illustrates the relationship between the position of line 1001 and the position of line 1001. Figure 9A The surface roughness of those points is significantly higher than that at the bottom of one of these point-like structures. For example, Figure 10A and 10B The dots in the image have a maximum height of 3.572 μm above the surface, for example, 0 μm, and a minimum height of -11.427 μm below the surface, for example, spanning a range of about 15 micrometers.

[0148] These two examples illustrate laser illumination, which involves continuous illumination of a lens surface as the laser scans each discrete path. However, other illumination schemes are also possible. For instance, in some cases, the laser can be pulsed while scanning along a discrete path. Examples of this are... Figure 11A As shown in the figure, Figure 11A A helical path 1101 is shown. As the laser scans along path 1101, the laser is pulsed, thereby producing multiple individual irradiation areas. The helical path is wound sufficiently tightly relative to the focal spot size, such that the irradiation areas overlap along the path and also overlap with irradiation areas in adjacent loops of the helix. The result is approximately circular dots with relatively smooth bottoms. Furthermore, such an irradiation scheme enables a lower overall laser dose delivered to the lens region, resulting in shallower dots compared to forming dots with a single continuous irradiation.

[0149] An example of point-like structures formed using a spiral path and pulsed laser. Figure 11B As shown in the figure, Figure 11B A top view of three such point-like objects is shown. Figure 11C The diagram shows the cross-sectional profile of one of the point objects, such as its height and along... Figure 11B The relationship between the position of line 1103 and the surface. In this example, the maximum height of the point is 1.466 μm above the surface, and the minimum height is approximately -4.363 μm. The bottom roughness through this section is only slightly less than the depth, but considering how shallow the point is, the bottom as a whole has relatively small roughness. In other words, although the fluctuation dF is not much smaller than the depth D, the depth D is quite shallow, and the absolute value of dF is small.

[0150] Laser formation on a dot matrix can lead to a phenomenon known as "burn-in," where the initial irradiation position at the start of the laser path results in a deeper portion of the dot matrix compared to the rest of the dot matrix. Such burn-in can manifest as a groove on one side of the dot matrix. The asymmetry caused by such burn-in grooves can lead to asymmetric scattering from different parts of the dot matrix. In some implementations, for example, where burn-in is unavoidable, it may be desirable to form burn-in grooves symmetrically at different locations within the dot matrix to reduce asymmetric scattering. Furthermore, the location of the burn-in grooves can vary for different dots across the lens to reduce or harness the overall asymmetry of scattering in areas of reduced contrast in the lens.

[0151] Such an example will now be described with reference to Figures 12A to 12C. Figure 12A shows a plan view of a lens 1200 having a region 1208 of reduced contrast surrounding a sharp aperture 1212. The reduced contrast region 1208 includes dots 1216 arranged in a radial array pattern. Each dot 1216 includes a recess formed in the surface 1220 of the lens 1200 using a symmetrical burn-in technique that creates two grooves on opposite sides of the dot.

[0152] This is shown in Figure 12B and Figure 12C The middle figure shows that Figure 12B and Figure 12C Plan views of a portion of the reduced-contrast region 1208 and cross-sections through one of the point features are shown. Each point feature 1216 includes a first sidewall 1224, a second sidewall 1128, and a central region 1232 between sidewalls 1224 and 1228. Depth profile ( Figure 12C The image shows a depression created by laser radiation during dot formation, which includes grooves 1236 and 1240 adjacent to sidewalls 1224 and 1228, respectively.

[0153] The depth D1 of the first trench 1236 is substantially equal to the depth D2 of the second trench 1240. The depth D3 of the central region 1232 disposed between the first trench 1236 and the second trench 1240 is less than the depth D1 of the first trench 1236 and the depth D2 of the second trench 1240.

[0154] As used herein, a "groove" can include a recess, channel, cavity, or fossa having a depth greater than that of adjacent portions. Typically, grooves on opposite sides of a point can have the same depth or different depths.

[0155] As shown in Figure 12B, the width of the trenches is not constant around the perimeter of the dots. Instead, each trench is crescent-shaped, having a widest portion corresponding to section C and a narrowest portion passing through a section perpendicular to C. The orientation of the crescent-shaped trenches is aligned with the radial direction of the dot array in the reduced contrast region 1208. This variation in trench alignment provides increased overall uniformity of average light scattering across the reduced contrast region.

[0156] Figure 12C The varying depth profiles shown in the illustration can be formed in various ways using laser burning. Figure 13The figure illustrates a first example method 1300 for forming a dot 1216 with a symmetrical depth profile. In this method 1300, the laser irradiation time at various locations of the dot 1216 is controlled to produce symmetrical burn-in recesses. Initially, a first step 1304 of method 1300 includes a laser beam from a focused laser system. A second step 1308 of method 1300 includes exposing a first location of an ophthalmic lens 1200 of lens material to focused laser radiation from the laser beam. Specifically, when a new dot 1216 is formed in the surface 1220 of the lens 1200, the laser exposes the lens surface 1220 to an initial burst of strong laser radiation, thereby producing initial burn-in defining a first sidewall 1224 and a first groove 1236 disposed inward relative to the first sidewall 1224. In a third step 1312, method 1300 includes inducing a relative movement between the laser beam and the lens away from the first groove 1236 in a first direction M while exposing the lens 1200 to focused laser radiation. In some examples, the laser moves away from the first sidewall 1224 in the M direction relative to the lens 1200 to continue forming the remainder of the dot-shaped recess. As the laser moves in the M direction, the lens 1200 is continuously exposed to focused laser radiation from the laser beam, resulting in the burning into the central region 1232 defining the dot-shaped recess 1216. The intensity of the laser beam is weaker than the initial burst of laser radiation during the formation of the central region 1232, and therefore the depth D3 of the central region 1232 is less than the depth D1 of the first groove 1236.

[0157] In the fourth step 1316, method 1300 includes exposing a second location of the ophthalmic lens to focused laser radiation to form a second sidewall 1228 and a second groove 1240 disposed inwardly relative to the second sidewall 1228 of the dot 1216. Again, because the intensity of the laser is weaker than the initial burst of radiation, the laser is paused for a period of time to expose the second groove 1240 to sufficient radiation to produce burn-in of depth D2 substantially equal to the depth D1 of the first groove 1236. Accordingly, the lens 1200 is exposed at the second groove 1240 to the laser beam for a period of time greater than the initial irradiation at the first groove 1236.

[0158] In some examples, the intensity of the laser beam is controlled to produce symmetrical burn-in recesses. In this example, the laser beam exposes lens 1200 to a first laser intensity to create a first groove 1236, and exposes different locations of lens 1200 to the first laser intensity to create a second groove 1240.

[0159] In some examples, the intensity and irradiation time are controlled to produce symmetrical burn-in depressions. In another example, laser irradiation can be pulsed to produce short, intense bursts of laser radiation, thereby forming a first and second trench of dot-like features before the central region is formed.

[0160] In some cases, dot patterns include randomly displaced dots relative to a regular array. Introducing random displacement can reduce optical effects associated with regularly spaced scattering centers, such as starburst glare. See, for example, https: / / www.slrlounge.com / diffraction-aperture-and-starburst-effects / , which illustrates the starburst effect related to photography. Accordingly, including random displacement in a dot pattern can provide a more comfortable experience for the user compared to a similar dot pattern in which the scattering centers are uniformly spaced. Alternatively or additionally, randomization of the dot pattern can reduce optical effects (e.g., diffraction or interference effects) manifested in reflected light, thereby reducing the dot pattern's attenuation to the observer.

[0161] refer to Figure 14 Example dot pattern 1400 includes an annular region 1404 surrounding a clear aperture 1408. The annular region has dots 1412 arranged in pattern 1400, including a radial direction B and a circumferential direction C. Specifically, the dots 1412 are arranged along a plurality of radial arrays 1416 relative to the clear aperture 1408 and in spaces 1420 between the different radial arrays 1416. Specifically, dots 1412A of a first size are arranged along the radial arrays 1416, and dots 1412B of different sizes are arranged in the spaces 1420 between the radial arrays 1416. According to pattern 1400, the dot size changes when moved in the circumferential direction C, and remains consistent when moved in the radial direction B.

[0162] Pattern 1400 also includes a second annular region 1424 within the annular region 1404 and adjacent to the hole 1408, wherein the dot 1412A is of a first size. In the second annular region 1424, the dot size is constant in both the radial direction B and the circumferential direction C2. However, in other examples, pattern 1400 may include only one annular region or more than two annular regions with varying dot patterns.

[0163] Figure 15Another example of a dot pattern 1500 includes an annular region 1504 surrounding a clear aperture 1508. The annular region 1504 has spaced-apart dots 1512 arranged in a pattern including a radial direction E and a circumferential direction F. Specifically, the dots 1512 are arranged relative to the aperture 1508 along a plurality of radial arrays 1516 and in spaces 1520 between the different radial arrays 1516. Specifically, dots 1512A of a first size are arranged along the radial arrays 1516, and dots 1512B of different sizes are arranged in the spaces 1520 between the radial arrays 1516 within the first annular region 1504. According to pattern 1500, the dot size changes when moved in the circumferential direction F, and remains consistent when moved in the radial direction E.

[0164] Pattern 1500 also includes a second annular region 1524 adjacent to the hole 1508 within the annular region 1504, wherein the dot 1512A is of a first size. In the second annular region 1524, the size of the dot is uniform in both the radial direction E and the circumferential direction F2.

[0165] exist Figure 16 In another example, a dot pattern 1600 for ophthalmic lenses includes an annular region 1604 of reduced contrast surrounding a clear aperture 1608. The annular region 1604 has spaced-apart dots 1612 to scatter incident light. The dots 1612 are arranged in a pattern including a radial direction G and a circumferential direction H. Specifically, a plurality of dots 1612 are arranged relative to the aperture 1608 along a plurality of radial arrays 1616 and in spaces 1620 between different radial arrays 1616. Dots 1612A of a first size are arranged along the radial arrays 1616, and second, smaller-sized dots 1612B are arranged in the spaces 1620 between the radial arrays 1616 within the first annular region 1604 of reduced contrast. According to pattern 1600, the dot size changes when moved in the circumferential direction H, and remains consistent when moved in the radial direction G.

[0166] Pattern 1600 also includes a second annular region 1624 adjacent to hole 1608, wherein third-sized dots 1612C are arranged between first-sized dots 1612A. In the second annular region 1624, the dot size varies along the circumferential direction H2. The third-sized dots 1612C are arranged in different patterns, including irregular variations in the spacing between adjacent dots 1612A. In the illustrated example, the third-sized dots 1612C are randomly arranged between radial arrays 1616. However, in other examples, the third-sized dots 1612C (e.g., smaller than dots 1612A and 1612B) may be uniformly spaced between adjacent dots 1612A, 1612C. In yet another example, the second-sized dots 1612B may also be arranged adjacent to dots 1612A, 1612C of other sizes.

[0167] Although compared to Figure 12A, Figure 14 , Figure 15 and Figure 16 The aforementioned example dotted pattern is composed of freely spaced dots, but patterns with overlapping dots are also possible. For example, see reference... Figure 17 Example dot pattern 1700 includes an annular region 1704 of reduced contrast surrounding a sharp aperture 1708, and overlapping dots 1712 for scattering incident light in the annular region 1704 of reduced contrast. The dots 1712 are arranged in a random pattern 1700 and have a uniform size. In some cases, one dot overlaps with another dot, and in others, with two or more other dots. The dots 1712 may simply contact or overlap each other to varying degrees (e.g., overlapping from about 1% to about 99% in the dot surface region). For example, the point overlap, determined by the percentage of the area of ​​the point that overlaps with one or more other point objects, can be 5% or greater (e.g., 10% or greater, 15% or greater, 20% or greater, 25% or greater, 30% or greater, 35% or greater, 40% or greater, 45% or greater, 50% or greater, 55% or greater, 60% or greater, 65% or greater, 70% or greater, 75% or greater, 80% or greater, 85% or greater, 90% or greater, or 95% or greater).

[0168] Figure 18Another example of a dot pattern 1800 includes a ring-shaped area 1804 of reduced contrast surrounding a sharp aperture 1808 and overlapping dots 1812 for scattering light within the reduced contrast area. The dot pattern 1800 includes a grid of vertical rows 1814 and columns 1818. In the illustrated example, dots 1812 arranged in row 1814 overlap with adjacent dots 1812 in the same row 1814. However, dots 1812 in column 1818 do not overlap with adjacent dots 1812 in the same column 1818. Multiple dots 1812 can simply touch or overlap each other to varying degrees (e.g., overlapping by area from about 1% to about 99%).

[0169] exist Figure 19 In another example, dot pattern 1900 includes an annular region 1904 of reduced contrast surrounding dot 1912 with a sharp aperture 1908 to scatter incident light in the reduced contrast region. Dot pattern 1900 includes a grid of rows 1914 and columns 1918, wherein dots 1912 arranged in rows 1914 overlap with adjacent dots 1912 in the same row 1914, and dots 1912 arranged in columns 1918 overlap with adjacent dots 1912 in the same column 1918. In the illustrated example, some dots 1912 do not overlap with adjacent dots 1912 in the same row (e.g., row 1914A), and some dots 1012 do not overlap with adjacent dots 1912 in the same column (e.g., column 1918A). In some rows 1914 and columns 1918 (e.g., row 1914B, column 1918B), some points 1912 overlap with adjacent points 1912 in both the same column 1918 and the same row 1914. Multiple points 1912 may simply touch or overlap each other to varying degrees (e.g., overlap by area from about 1% to about 99%).

[0170] exist Figure 20Another example of a dot pattern 2000 for an ophthalmic lens includes a region of reduced contrast consisting of a first annular region 2004 and a second annular region 2024 surrounding a clear aperture 2008, and overlapping dots 2012 for scattering incident light in the first annular region 2004 and the second annular region 2024. The dot pattern 2000 includes a plurality of dots arranged both radially and circumferentially relative to the aperture 2008. Specifically, the plurality of dots 2012 are arranged relative to the aperture 2008 along a plurality of radial arrays 2016 and overlapping in a space 2020 between different radial arrays 2016. A plurality of dots 2012A of a first size are arranged along the radial arrays 2016 in the two annular regions 2004, 2024, and a plurality of dots 2012B of different sizes are disposed in the space 2020 between the radial arrays 2016 and within the first annular region 2004. Pattern 2000 also includes a second annular region 2024 adjacent to hole 2008, wherein dot 2012A is of a first size. In some cases, dot 2012 overlaps with adjacent dot 2012 of the same and / or different sizes. In some cases, one dot 2012 overlaps with another dot 2012, and in other cases, overlaps with two or more other dot 2012. Multiple dot 2012 may simply contact or overlap each other to varying degrees (e.g., from about 1% to about 99% overlap). In other cases, dot 2012 does not overlap with any other dot 2012.

[0171] exist Figure 21 In another example, the dot pattern 2100 for an ophthalmic lens includes a region with reduced contrast having a first annular region 2104 and a second annular region 2124 surrounding a clear aperture 2108, and dots 2112 in the first and second annular regions 2104 and 2124. In the first annular region 2104, some of the dots 2112 of varying sizes overlap with adjacent dots 2112 of the same or different sizes. In the second annular region 2124, the dots 2112 have a uniform size and do not overlap with adjacent dots 2112. In some cases, the dots 2112 overlap with adjacent dots 2112 of the same and / or different sizes. In some cases, one dot 2112 overlaps with another dot 2112, and in other cases, it overlaps with two or more other dots 2112. Multiple overlapping points 2112 can simply touch or overlap each other to varying degrees (e.g., by area, from about 1% to about 99%).

[0172] Figure 22The illustration shows another example dot pattern 2200 for ophthalmic lenses, comprising regions with reduced contrast having a first annular region 2204, a second annular region 2224, and a third annular region 2228. The third annular region 2228 surrounds a clear aperture 2208 and has overlapping dots 2212 of different sizes 2212A, 2212B, 2212C arranged in a random pattern. In some cases, the dots 2212 overlap with adjacent dots 2212 of the same and / or different sizes. The dots 2212 in the second annular region 2224 do not overlap, and the dots 2212 in the first annular region 2228 overlap with one or more adjacent dots 2212. In some cases, one dot 2212 in the first annular region 2204 and the third annular region 2228 overlaps with another dot 2212, and in other cases, overlaps with two or more other dots 2212. Multiple overlapping points 2212 can simply touch or overlap each other to varying degrees (e.g., by area, from about 1% to about 99%).

[0173] In some examples, the dot pattern is characterized by, for example, a gradient in the size and / or spacing of the dots. The dot pattern can also be characterized by a gradient in the scattering efficiency of the dots (e.g., due to refractive index mismatch and / or shape gradients of each dot). A graded dot pattern can reduce the conspicuousness of the pattern. For example, a graded transition from the sharp portion of the lens to the scattering portion can be less noticeable than a sharp transition.

[0174] In addition to the embodiments described in the appended claims and the embodiments described above, the embodiments numbered below are also novel.

[0175] Example 1 is an ophthalmic lens comprising: a lens body having a pair of opposing curved surfaces; a plurality of discrete light scattering centers arranged in a region of at least one of the opposing curved surfaces, each scattering center having a shape at least partially defined by a peripheral shape, a maximum depth D and a maximum width W, wherein the ratio D / W is 1 / 5 or less.

[0176] Example 2 is an ophthalmic lens comprising: a lens body having a pair of opposing curved surfaces; a plurality of discrete light scattering centers arranged in a region of at least one of the opposing curved surfaces, each scattering center having a shape at least partially defined by a peripheral shape, a maximum depth D and a maximum width W, wherein D is 20 micrometers (μm) or less and W is 100 μm or greater.

[0177] Example 3 is an ophthalmic lens, comprising: a lens body having a pair of opposing curved surfaces defining a lens axis; a plurality of discrete light scattering centers arranged in a region of at least one of the opposing curved surfaces, each scattering center having a recess and a bottom, the recess having a maximum depth D and a maximum width W, and the bottom having a minimum width W. floor and maximum depth change δD floor W floor It is 0.5W or greater, and δD floor It is 0.2D or smaller.

[0178] Example 4 is an ophthalmic lens comprising: a lens body having a pair of opposing curved surfaces defining a lens axis; and a plurality of discrete light scattering centers arranged in a region of at least one of the opposing curved surfaces, each scattering center having a shape at least partially defined by a peripheral shape, a maximum depth, and a maximum width, wherein the peripheral shape is selected from the group consisting of a star, a regular polygon, a dumbbell, a pear, a parallelogram, a crescent, a cone, and a serrated shape.

[0179] Example 5 is an ophthalmic lens comprising: a lens body having a pair of opposing curved surfaces; a plurality of discrete light scattering centers arranged in a region of at least one of the opposing curved surfaces, wherein the density and shape of the light scattering centers in the region are selected such that for light incident on the region of the lens and propagating parallel to the lens axis, 12% or less and 50% or more of the backscattered light incident on the region of the ophthalmic lens is forward scattered into a solid angle of 5 degrees.

[0180] Example 6 is an ophthalmic lens according to any of the foregoing embodiments, wherein the region surrounds a clear region without a scattering center.

[0181] Example 7 is an ophthalmic lens according to any of the foregoing embodiments, wherein the region is a ring-shaped region.

[0182] Example 8 is an ophthalmic lens according to any of the foregoing embodiments, wherein the light scattering center is formed on a single surface of the ophthalmic lens.

[0183] Example 9 is an ophthalmic lens according to any one of Examples 1 to 7, wherein the light scattering center is formed only on a single surface of the ophthalmic lens.

[0184] Example 10 is an ophthalmic lens according to Example 9, wherein the single surface is a concave surface.

[0185] Example 11 is an ophthalmic lens according to Example 9, wherein the single surface is a convex surface.

[0186] Example 12 is an ophthalmic lens according to any of the foregoing embodiments, wherein each of the light scattering centers has the same shape.

[0187] Example 13 is an ophthalmic lens according to any one of Examples 1 to 11, wherein at least some of the light scattering centers have different shapes.

[0188] Example 14 is an ophthalmic lens according to any of the foregoing embodiments, wherein the ophthalmic lens is a spectacle lens or a contact lens.

[0189] Example 15 is an ophthalmic lens according to any of the foregoing examples, wherein the ophthalmic lens is a plano lens, a single-vision lens, or a multifocal lens.

[0190] Example 16 is a method comprising: exposing a surface of an ophthalmic lens to one or more laser radiation pulses sufficient to generate light scattering centers in the surface; and moving the laser radiation relative to the surface while exposing the surface to trace a path on the surface, wherein the path is helical and the light scattering centers have a maximum width W in the range of 100 micrometers to 1,000 micrometers.

[0191] Example 17 is a method comprising: exposing a surface of an ophthalmic lens to one or more laser radiation pulses sufficient to generate light scattering centers in the surface; and moving the laser radiation relative to the surface while exposing the surface to trace a path on the surface, wherein the light scattering centers have a maximum width W in the range of 100 micrometers to 1,000 micrometers and a peripheral shape selected from the group consisting of a star, a regular polygon, a dumbbell, a pear, a parallelogram, a crescent, a cone, and a serrated shape.

[0192] Example 18 is an ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular region surrounding a clear aperture, wherein the annular region has a plurality of light scattering centers in the lens body and / or on at least one of the two opposing surfaces, the size and shape of the plurality of light scattering centers being designed to scatter incident light, wherein a first light scattering center among the plurality of light scattering centers overlaps with an adjacent light scattering center.

[0193] Example 19 is an ophthalmic lens according to Example 18, wherein the light scattering centers are arranged in a pattern including rows, wherein the first light scattering center and the adjacent light scattering centers are arranged in a row.

[0194] Example 20 is an ophthalmic lens according to Example 19, wherein the light scattering centers are arranged in a pattern including columns.

[0195] Example 21 is an ophthalmic lens according to Example 20, wherein the second light scattering center and the third light scattering center overlap in a row.

[0196] Example 22 is an ophthalmic lens according to Example 20 or 21, wherein the first light scattering center overlaps with different light scattering centers, and the first light scattering center and the different light scattering centers are arranged in a row.

[0197] Example 23 is an ophthalmic lens according to Example 18, wherein the first light scattering center is of a first size, and the first adjacent light scattering center is of a second size different from the first size.

[0198] Example 24 is an ophthalmic lens according to Example 18, wherein the light scattering center is arranged in a pattern including a circumferential direction and a radial direction relative to the clear aperture.

[0199] Example 25 is an ophthalmic lens according to Example 18, wherein the light scattering centers are arranged in a pattern of irregular variations including the spacing between adjacent light scattering centers.

[0200] Example 26 is an ophthalmic lens according to any one of Examples 18 to 25, comprising a second annular region, wherein the light scattering centers disposed in the second annular region do not overlap.

[0201] Example 27 is an ophthalmic lens according to Example 18, wherein the ophthalmic lens has a lens axis, and the aperture and annular region are substantially centered on the lens axis.

[0202] Example 28 is an ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular region surrounding a clear aperture, wherein the annular region has a plurality of spaced-apart light scattering centers in the lens body and / or on at least one of the two opposing surfaces, the plurality of spaced-apart light scattering centers being sized and shaped to scatter incident light, the light scattering centers being arranged in a pattern including a circumferential direction and a radial direction relative to the clear aperture, wherein the light scattering centers arranged along the radial direction have a first size, and the light scattering centers arranged along the circumferential direction have a second size different from the first size.

[0203] Example 29 is an ophthalmic lens according to Example 28, wherein the first size is uniform and the second size is variable.

[0204] Example 30 is an ophthalmic lens according to Example 28, including a second annular region disposed between the clear aperture and the annular region, wherein the light scattering center disposed in the second annular region is the same size in both the radial direction and the circumferential direction.

[0205] Example 31 is an ophthalmic lens according to Example 28, wherein a portion of the light scattering centers are arranged in different patterns including irregular variations in the spacing between adjacent light scattering centers.

[0206] Example 32 is an ophthalmic lens according to Example 28, wherein the shape of the light scattering center is substantially circular.

[0207] Example 33 is an ophthalmic lens according to Example 28, wherein the lens has a lens axis and the clear aperture and annular region are substantially centered on the lens axis.

[0208] Example 34 is an ophthalmic lens according to Example 28, wherein the lens is a spectacle lens or a contact lens.

[0209] Example 35 is an ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular region surrounding a clear aperture, wherein the annular region has a plurality of spaced-apart light scattering centers in the lens body and / or on at least one of the two opposing surfaces, the plurality of spaced-apart light scattering centers being sized and shaped to scatter incident light, the plurality of light scattering centers being arranged in a pattern including a circumferential direction and a radial direction relative to the clear aperture, wherein the light scattering centers arranged along the radial direction have a uniform size, and the light scattering centers arranged along the circumferential direction have different sizes.

[0210] Example 36 is an ophthalmic lens according to Example 35, including a second annular region disposed between the clear aperture and the annular region, wherein the light scattering center disposed in the second annular region is the same size in both the radial direction and the circumferential direction.

[0211] Example 37 is an ophthalmic lens according to Example 28, wherein a portion of the light scattering centers are arranged in different patterns including irregular variations in the spacing between adjacent light scattering centers.

[0212] Example 38 is an ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular region surrounding a clear aperture, wherein the annular region has a plurality of spaced-apart light scattering centers on at least one of the two opposing surfaces, the plurality of spaced-apart light scattering centers being sized and shaped to scatter incident light, each light scattering center including a recess in one of the surfaces, wherein one or more of the light scattering centers have a depth profile relative to the one surface, the depth profile including a first groove positioned toward a first sidewall of the recess and a second groove positioned toward a second sidewall of the recess.

[0213] Example 39 is an ophthalmic lens according to Example 38, wherein the depth profile of the recess is symmetrical about at least one plane.

[0214] Example 40 is an ophthalmic lens according to Example 38, wherein the depth profile of the recess is axially symmetrical.

[0215] Example 41 is an ophthalmic lens according to Example 38, wherein the maximum depth of the first groove is substantially equal to the maximum depth of the second groove.

[0216] Example 42 is an ophthalmic lens according to Example 41, wherein the region between the first groove and the second groove of the one or more light scattering centers has a depth different from the maximum depth of the first groove and the maximum depth of the second groove.

[0217] Example 43 is an ophthalmic lens according to Example 38, wherein the orientation of the grooves in different light scattering centers in the light scattering center varies at different positions in the annular region.

[0218] Example 44 is an ophthalmic lens according to any one of Examples 38 to 43, wherein the one or more light scattering centers have a circular peripheral shape.

[0219] Example 45 is an ophthalmic lens according to any one of Examples 38 to 44, wherein the maximum width in the light scattering center is in the range of 100 micrometers (μm) to 1,500 μm.

[0220] Example 46 is an ophthalmic lens according to any one of Examples 38 to 45, wherein the radial dimension of the first groove is 0.3W or less, where W is the maximum width among the plurality of light scattering centers.

[0221] Example 47 is an ophthalmic lens according to any one of Examples 38 to 46, wherein the depth profile includes one or more additional grooves between the first groove and the second groove.

[0222] Example 48 is a method comprising: exposing a first location of an ophthalmic lens material to focused laser radiation from a laser beam to form a first sidewall of an optical scattering feature on the surface of the ophthalmic lens; causing relative motion between the laser beam and the lens in a first direction away from the first sidewall while exposing the lens to the focused laser radiation; and exposing a second location of the ophthalmic lens to the focused laser radiation to form a second sidewall of the optical scattering feature, wherein the exposure of the first and second locations of the ophthalmic lens creates a recess in the lens material, the recess having a depth profile relative to the surface of the ophthalmic lens, the depth profile including a first groove of dots positioned toward the first sidewall and a second groove positioned toward the second sidewall.

[0223] Example 49 is the method according to Example 48, wherein exposing the first position includes exposing the first position of the lens for a first time period, and wherein exposing the second position includes exposing the second position for a second time period longer than the first time period.

[0224] Example 50 is the method according to Example 48 or 49, wherein the first sidewall and the second sidewall form a round optical scattering feature.

[0225] Example 51 is a method according to any one of Examples 48 to 50, wherein the depth of the first trench is substantially equal to the depth of the second trench.

[0226] Example 52 is a method according to any one of Examples 48 to 51, wherein relative motion is caused to create a region having a depth different from the depth of the first groove and the second groove between one or more point-like objects.

[0227] Example 53 is an ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular region surrounding a clear aperture, wherein the annular region has a plurality of light scattering centers in the lens body and / or on at least one of the two opposing surfaces, the size and shape of the plurality of light scattering centers being designed to scatter incident light, wherein at least some of the plurality of light scattering centers have diameters ranging from about 1.001 mm to about 1.5 mm, and the spacing between the dots varies across the annular region.

[0228] Example 54 is an ophthalmic lens according to Example 53, wherein the light scattering centers are arranged in a pattern including a circumferential direction and a radial direction relative to the clear aperture, wherein the light scattering centers arranged along the radial direction have a uniform size and the light scattering centers arranged along the circumferential direction have a variable size.

[0229] Example 55 is an ophthalmic lens according to Example 53, including a second annular region disposed between the clear aperture and the annular region, wherein the light scattering center disposed in the second annular region is the same size in both the radial direction and the circumferential direction.

[0230] Example 56 is an ophthalmic lens according to Example 53, wherein the first light scattering center among the plurality of light scattering centers overlaps with the adjacent light scattering center.

[0231] Example 57 is an ophthalmic lens according to Example 56, wherein the light scattering centers are arranged in a pattern including rows, wherein the first light scattering center and the adjacent light scattering centers are arranged in a row.

[0232] Example 58 is an ophthalmic lens according to Example 57, wherein the light scattering centers are arranged in a pattern including columns.

[0233] Example 59 is an ophthalmic lens according to Example 53, wherein the light scattering centers are arranged in a pattern that includes an irregular variation in the spacing between the adjacent scattering centers.

[0234] Example 60 is an ophthalmic lens according to Example 53, wherein each light scattering center includes a recess in one surface of the ophthalmic lens, wherein one or more of the light scattering centers have a depth profile relative to the one surface of the ophthalmic lens, the depth profile including a first groove positioned toward a first sidewall of the light scattering center and a second groove positioned toward a second sidewall of the light scattering center.

[0235] Example 61 is an ophthalmic lens according to Example 60, wherein the depth profile of the one or more light scattering centers is symmetrical.

[0236] Example 62 is an ophthalmic lens according to Example 60, wherein the depth of the first groove is substantially equal to the depth of the second groove.

[0237] While this specification contains numerous details of specific implementations, these should not be construed as limiting the scope of any disclosure or claimable content, but rather as descriptions of features specific to particular examples that may be specific to a particular disclosure. Some features described herein in the context of separate examples can also be implemented in combination in a single example. Conversely, various features described in the context of a single example can also be implemented separately or in any suitable sub-combination in multiple examples. Furthermore, although features may be described herein as functioning in certain combinations and even initially claimed in this way, one or more features from a claimed combination can be removed from that combination in some cases, and the claimed combination may be for sub-combinations or variations thereof.

[0238] Similarly, although operations are depicted in a specific order in the accompanying drawings, this should not be construed as requiring such operations to be performed in the specific order shown or in sequential order, or to perform all the illustrated operations to achieve the desired result. In some cases, multitasking and parallel processing may be advantageous. Furthermore, the separation of various system modules and components in the examples described herein should not be construed as requiring such separation in all examples, and it should be understood that the described program components and systems can generally be integrated together in a single product or assembled into multiple products.

[0239] Specific examples of the subject matter have been described. Other examples are within the scope of the following claims. For example, the actions recited in the claims can be performed in different orders and still achieve the desired result. As an example, the processes depicted in the drawings do not necessarily require the specific order or sequence shown to achieve the desired result. In some embodiments, multitasking and parallel processing may be advantageous.

Claims

1. An ophthalmic lens comprising: a lens body having a pair of opposing curved surfaces; and a plurality of discrete light scattering centers disposed in a region of at least one of the opposing curved surfaces, each scattering center having a shape defined at least in part by a perimeter shape, a maximum depth D, and a maximum width W, wherein the ratio D / W is 1 / 5 or less.

2. An ophthalmic lens comprising: a lens body having a pair of opposing curved surfaces; and a plurality of discrete light scattering centers disposed in a region of at least one of the opposing curved surfaces, each scattering center having a shape defined at least in part by a perimeter shape, a maximum depth D, and a maximum width W, wherein D is 20 microns (pm) or less and W is 100 pm or more.

3. An ophthalmic lens comprising: a lens body having a pair of opposing curved surfaces defining a lens axis; and a plurality of discrete light scattering centers arranged in a region of at least one of the opposing curved surfaces, each scattering center having a recess with a maximum depth D and a maximum width W, and a base with a minimum width W floor and a maximum depth variation δD floor , where W floor is 0.5W or more, and δD floor is 0.2D or less.

4. An ophthalmic lens comprising: a lens body having a pair of opposing curved surfaces defining a lens axis; and a plurality of discrete light scattering centers disposed in a region of at least one of the opposing curved surfaces, each scattering center having a shape defined at least in part by a perimeter shape, a maximum depth, and a maximum width, wherein the perimeter shape is selected from the group consisting of a star shape, a regular polygon shape, a dumbbell shape, a pear shape, a parallelogram shape, a crescent shape, a cone shape, and a zigzag shape.

5. An ophthalmic lens comprising: a lens body having a pair of opposing curved surfaces; and a plurality of discrete light scattering centers disposed in a region of at least one of the opposing curved surfaces, wherein the density of the plurality of light scattering centers in the region and the shape of the plurality of light scattering centers are selected such that, for light incident on the region of the ophthalmic lens that is propagating parallel to the lens axis, the ophthalmic lens backscatters 12% or less of the light incident on the region.

6. The ophthalmic lens of claim 1, wherein, The region is surrounded by a clear region free of scattering centers.

7. The ophthalmic lens of claim 1, wherein, The region is an annular region.

8. The ophthalmic lens of claim 1, wherein, The plurality of light scattering centers are formed on a single surface of the ophthalmic lens.

9. The ophthalmic lens of claim 1, wherein, The plurality of light scattering centers are formed on only a single surface of the ophthalmic lens.

10. The ophthalmic lens of claim 9, wherein, The single surface is a concave surface.

11. The ophthalmic lens of claim 9, wherein, The single surface is a convex surface.

12. The ophthalmic lens of claim 1, wherein, Each of the plurality of light scattering centers has the same shape.

13. The ophthalmic lens of claim 1, wherein, At least some of the plurality of light scattering centers have different shapes.

14. The ophthalmic lens of claim 1, wherein, The ophthalmic lens is an eyeglass lens or a contact lens.

15. The ophthalmic lens of claim 1, wherein, The ophthalmic lens is a piano lens, a single vision lens, or a multifocal lens.

16. A method comprising: exposing a surface of an ophthalmic lens to one or more pulses of laser radiation sufficient to produce light scattering centers in the surface; and moving the laser radiation relative to the surface while the surface is exposed to delineate a path on the surface, wherein the path has a spiral shape and the light scattering centers have a maximum width W in a range from 100 microns to 1,000 microns.

17. A method comprising: exposing a surface of an ophthalmic lens to one or more pulses of laser radiation sufficient to produce light scattering centers in the surface; and moving the laser radiation relative to the surface while the surface is exposed to delineate a path on the surface, wherein the light scattering centers have a maximum width W in a range from 100 microns to 1,000 microns and a perimeter shape selected from the group consisting of star-shaped, regular polygonal, dumbbell-shaped, pear-shaped, parallelogram-shaped, crescent-shaped, conical, and zigzag-shaped.

18. An ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular zone surrounding a clear aperture, wherein the annular zone has a plurality of light scattering centers sized and shaped to scatter incident light, wherein a first light scattering center of the plurality of light scattering centers overlaps a first adjacent light scattering center by a first amount and overlaps a second adjacent light scattering center by a second amount different from the first amount.

19. The ophthalmic lens of claim 18, wherein, the light scattering centers are arranged in a pattern comprising rows, wherein the first light scattering center and the first adjacent light scattering center are disposed in a row.

20. The ophthalmic lens of claim 19, wherein, the light scattering centers are arranged in a pattern comprising columns.

21. The ophthalmic lens of claim 20, wherein, a second light scattering center overlaps a third light scattering center in a column.

22. The ophthalmic lens of claim 20, wherein, the first light scattering center overlaps a different light scattering center and the first light scattering center and the different light scattering center are disposed in a column.

23. The ophthalmic lens of claim 18, wherein, the first light scattering center is a first size and the first adjacent light scattering center is a second size different from the first size.

24. The ophthalmic lens of claim 18, wherein, the light scattering centers are arranged in a pattern comprising a circumferential direction and a radial direction relative to the clear aperture.

25. The ophthalmic lens of claim 18, wherein, the light scattering centers are arranged in a pattern comprising irregular variation in spacing between pairs of adjacent light scattering centers.

26. The ophthalmic lens of claim 18, comprising a second annular zone, wherein, the light scattering centers disposed in the second annular zone do not overlap.

27. The ophthalmic lens of claim 18, wherein, the ophthalmic lens has a lens axis and the clear aperture and annular zone are substantially centered on the lens axis.

28. An ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular zone surrounding a clear aperture, wherein the annular zone has a plurality of spaced-apart light scattering centers sized and shaped to scatter incident light, the plurality of light scattering centers arranged in a pattern comprising a circumferential direction and a radial direction relative to the clear aperture, wherein the plurality of light scattering centers arranged along the radial direction have a first size and the plurality of light scattering centers arranged along the circumferential direction have a second size different from the first size.

29. The ophthalmic lens of claim 28, wherein, the first size is uniform and the second size is variable.

30. The ophthalmic lens of claim 28, comprising a second annular zone disposed between the clear aperture and the annular zone, wherein, the plurality of light scattering centers disposed in the second annular zone are uniform in size in both the radial direction and the circumferential direction.

31. The ophthalmic lens of claim 28, wherein, A portion of the plurality of light scattering centers are arranged in a different pattern that includes irregular variations in spacing between adjacent light scattering centers.

32. The ophthalmic lens of claim 28, wherein, The plurality of light scattering centers are substantially circular in shape.

33. The ophthalmic lens of claim 28, wherein, The ophthalmic lens has a lens axis and the clear aperture and annular zone are substantially centered on the lens axis.

34. The ophthalmic lens of claim 28, wherein, The ophthalmic lens is an eyeglass lens or a contact lens.

35. An ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular zone surrounding a clear aperture, wherein the annular zone has a plurality of spaced-apart light scattering centers sized and shaped to scatter incident light, the plurality of light scattering centers being arranged in a pattern that includes a circumferential direction and a radial direction relative to the clear aperture, wherein the plurality of light scattering centers arranged along the radial direction have a uniform size and the plurality of light scattering centers arranged along the circumferential direction have different sizes.

36. The ophthalmic lens of claim 35, comprising a second annular zone disposed between the clear aperture and the annular zone, wherein, The plurality of light scattering centers disposed in the second annular zone are uniform in size in both the radial direction and the circumferential direction.

37. The ophthalmic lens of claim 35, wherein, A portion of the plurality of light scattering centers are arranged in a different pattern that includes irregular variations in spacing between adjacent light scattering centers.

38. An ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular zone surrounding a clear aperture, wherein the annular zone has a plurality of light scattering centers on at least one of the two opposing surfaces, the plurality of light scattering centers being sized and shaped to scatter incident light, each light scattering center including a recess in one of the two opposing surfaces, wherein at least a portion of the plurality of light scattering centers has a depth profile relative to the one of the two opposing surfaces, the depth profile including a first groove positioned toward a first sidewall of the recess and a second groove positioned toward a second sidewall of the recess.

39. The ophthalmic lens of claim 38, wherein, The depth profile of the recess is symmetric about at least one plane.

40. The ophthalmic lens of claim 38, wherein, The depth profile of the recess is axially symmetric.

41. The ophthalmic lens of claim 38, wherein, A maximum depth of the first groove is substantially equal to a maximum depth of the second groove.

42. The ophthalmic lens of claim 41, wherein, An area between the first groove and the second groove of the plurality of light scattering centers has a different depth than the maximum depth of the first groove and the maximum depth of the second groove.

43. The ophthalmic lens of claim 38, wherein, An orientation of the groove in different ones of the light scattering centers varies at different locations of the annular zone.

44. The ophthalmic lens of claim 38, wherein, The plurality of light scattering centers have a circular peripheral shape.

45. The ophthalmic lens of claim 38, wherein, A maximum width of each of the plurality of light scattering centers is in a range from 100 micrometers (pm) to 1,500 pm.

46. The ophthalmic lens of claim 38, wherein, A radial dimension of the first groove is 0.3W or less, where W is a maximum width of one of the plurality of light scattering centers.

47. The ophthalmic lens of claim 38, wherein, The depth profile includes one or more additional grooves between the first groove and the second groove.

48. A method comprising: exposing a first location of an ophthalmic lens of a lens material to focused laser radiation of a laser beam to form a first sidewall of an optically scattering feature on a surface of the ophthalmic lens; causing relative motion between the laser beam and the ophthalmic lens in a first direction away from the first sidewall while the ophthalmic lens is exposed to the focused laser radiation; and exposing a second location of the ophthalmic lens to the focused laser radiation to form a second sidewall of the optically scattering feature, wherein exposing the first and second locations of the ophthalmic lens creates a recess in the lens material having a depth profile relative to the surface of the ophthalmic lens comprising a first trough of the recess positioned toward the first sidewall and a second trough of the recess positioned toward the second sidewall.

49. The method of claim 48, wherein, Exposing the first location includes exposing the first location of the ophthalmic lens for a first time period, and wherein exposing the second location includes exposing the second location for a second time period greater than the first time period.

50. The method of claim 48, wherein, The first and second sidewalls form a circular optically scattering feature.

51. The method of claim 48, wherein, The first trough has a depth substantially equal to a depth of the second trough.

52. The method of claim 48, wherein, Causing relative motion creates a region between the first and second troughs of the recess having a depth different from the depth of the first trough and the depth of the second trough.

53. An ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular zone surrounding a clear aperture, wherein the annular zone has a plurality of light scattering centers sized and shaped to scatter incident light, wherein at least some of the plurality of light scattering centers have a diameter in a range from about 1.001 mm to about 1.5 mm, and a spacing between the light scattering centers varies across the annular zone.

54. The ophthalmic lens of claim 53, the light scattering centers are arranged in a pattern comprising a circumferential direction and a radial direction relative to the clear aperture, wherein, the light scattering centers arranged along the radial direction have a uniform size, the plurality of light scattering centers arranged along the circumferential direction have a variable size.

55. The ophthalmic lens of claim 54, comprising a second annular zone disposed between the clear aperture and the annular zone, wherein, the light scattering centers disposed in the second annular zone are uniform in size in both the radial direction and the circumferential direction.

56. The ophthalmic lens of claim 53, wherein, a first light scattering center of the plurality of light scattering centers overlaps an adjacent light scattering center.

57. The ophthalmic lens of claim 56, wherein, the light scattering centers are arranged in a pattern comprising a row, wherein the first light scattering center and the adjacent light scattering center are disposed in a row.

58. The ophthalmic lens of claim 57, wherein, the plurality of light scattering centers are arranged in a pattern comprising a column.

59. The ophthalmic lens of claim 53, wherein, the plurality of light scattering centers are arranged in a pattern comprising irregular variation in spacing between the adjacent scattering centers.

60. The ophthalmic lens of claim 53, wherein, each light scattering center comprises a recess in one of the two opposing surfaces of the ophthalmic lens, wherein at least a portion of the plurality of light scattering centers has a depth profile relative to the one of the two opposing surfaces of the ophthalmic lens, the depth profile comprising a first groove positioned toward a first sidewall of the light scattering center and a second groove positioned toward a second sidewall of the light scattering center.

61. The ophthalmic lens of claim 60, wherein, The depth profile of the portion of the plurality of light scattering centers is symmetrical.

62. The ophthalmic lens of claim 60, wherein, A depth of the first groove is substantially equal to a depth of the second groove.

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