An ophthalmic lens with light scattering for treating myopia, and a method for manufacturing the same.

Abstract

Ophthalmic lenses for reducing the progression of myopia are disclosed, which include a scattering center with reduced backscatter, and which include various shapes and patterns for the scattering center. Methods for fabricating ophthalmic lenses and devices incorporating ophthalmic lenses are disclosed.

Description

Technical Field

[0001] The present invention features an ophthalmic lens for treating myopia and reducing the progression of myopia, as well as a method for manufacturing the same.

Background Art

[0002] The eye is an optical sensor where light from an external source is focused onto the surface of the retina (an array of wavelength-dependent photosensors) by a lens. Each of the various shapes that the eye's lens can adopt is associated with a focal length at which external light rays are focused optimally or nearly optimally, creating an inverted image on the surface of the retina that corresponds to the external image observed by the eye. In each of the various shapes that the eye's lens can adopt, the eye's lens optimally or nearly optimally focuses the light emitted (or reflected from an external object) by an external object within a specific distance range from the eye, and does not focus as optimally or at all on objects outside that distance range.

[0003] In an individual with normal vision, the axial length of the eye, or the distance from the lens to the surface of the retina, corresponds to the focal length for the nearly optimal focusing of distant objects. The eyes of an individual with normal vision focus on distant objects without neural input to the muscles (a process called "accommodation") that apply force to change the shape of the eye's lens. Closer neighboring objects are focused by a normal individual as a result of accommodation.

[0004] However, many people suffer from conditions related to the length of the eye (for example, myopia). In myopic individuals, the axial length of the eye is longer than the axial length required to focus on distant objects without accommodation. As a result, myopic individuals can see nearby objects clearly, but distant objects appear blurry. Myopic individuals can generally accommodate, but the average distance at which they can focus on objects is shorter than that for individuals with normal vision.

[0005] Typically, infants are born farsighted, with the length of the eye being shorter than necessary to optimally or nearly optimally focus on distant objects without accommodation. During normal eye development (referred to as "emmetropia"), the axial length of the eye increases to a length that, relative to other dimensions of the eye, provides nearly optimal focusing on distant objects without accommodation. Ideally, the biological process maintains a nearly optimal relative length of the eye to its size as the eye grows to its final adult size. However, in myopic individuals, the axial length of the eye relative to the overall eye size continues to increase during development, exceeding the length that provides nearly optimal focusing on distant objects, leading to increasingly pronounced myopia.

[0006] Myopia is thought to be influenced not only by genetic factors but also by behavioral factors. Therefore, myopia can be alleviated by therapeutic devices that address behavioral factors. For example, a therapeutic device for treating diseases related to the length of the eye (including myopia) is described in U.S. Patent Application Publication 2011 / 0313058A1. [Prior art documents] [Patent Documents]

[0007] [Patent Document 1] U.S. Patent Application Publication No. 2011 / 0313058 [Patent Document 2] U.S. Patent Application Publication No. 20190033619 [Patent Document 3] U.S. Patent Application Publication No. 2019 / 0235279 [Overview of the project] [Means for solving the problem]

[0008] Disclosed are eyeglasses that reduce the signals in the retina that cause growth of the eye length. Exemplary eyeglass lenses are made using polycarbonate or Trivex lens blanks treated by forming a pattern of scattering centers (or "dots") that voluntarily have dot-free apertures on the visual axis. The dots scatter incident light that would otherwise be focused by the lens, resulting in a reduction of contrast in the retinal image. This contrast reduction reduces eye length, which is associated with the progression of myopia, particularly in children. The voluntary apertures (dot-free) are typically positioned on the visual axis corresponding to the wearer's distance vision, allowing the user to experience maximum visual acuity when viewing on-axis objects, while objects at the periphery of the user's field of vision are seen with reduced contrast and visual acuity.

[0009] Controlling the dot size and shape is used to adjust the light scattering characteristics of the lens. One function is to increase forward scattering in a direction in which scattered light contributes to reduced image contrast in the wearer's peripheral vision. Another function is to reduce backscattered light. Reducing backscattered light can reduce the conspicuousness of the dot pattern. Increasing directional forward scattering can reduce the overall number of dots required to provide a therapeutic effect.

[0010] A laser exposure method useful for forming dots of a desired shape is also disclosed. This exposure method may include using a laser scanning path that can be efficiently implemented, and it is possible to increase the overall throughput of the laser system by reducing the exposure time or cycle time.

[0011] Among other advantages, the disclosed embodiments feature eyeglasses that include a feature that reduces signals in the retina causing growth of the length of the eye on the lenses for both eyes, without reducing the user's axial vision in either eye to an extent that impairs the user. For example, providing a dot pattern that moderately blurs the wearer's peripheral vision or reduces contrast while allowing normal axial vision through a clear aperture enables daily use by the wearer throughout the day. Furthermore, the disclosed embodiments make it possible to provide therapeutic benefits to the user in both eyes using only a single pair of eyeglasses, in contrast to approaches that involve the alternating use of different pairs of eyeglasses.

[0012] Furthermore, the dot pattern can be virtually unnoticeable to others, especially if the dot pattern is clear and colorless, and / or if contact lenses are used. The fineness of the dot pattern can result in more consistent use by certain wearers (particularly children) who may be concerned about being seen during the daily use of otherwise conspicuous devices (e.g., at school, or otherwise among peers). For example, a gradient dot pattern can be used to reduce the visibility of the dot pattern to third parties.

[0013] The disclosed embodiments can enable the efficient and economical formation of dot patterns for reducing eye lengthening on conventional ophthalmic lenses, for example, by forming the dot pattern on the surface of the lens or within the bulk.

Brief Description of the Drawings

[0014] [Figure 1A] A diagram showing an exemplary pair of glasses containing an ophthalmic lens for reducing the progression of myopia. [Figure 1B] A diagram showing the ophthalmic lens shown in FIG. 1A before edge processing. [Figure 1C] A plan view of the dot pattern in the reduced contrast region of the lens shown in FIG. 1B. [Figure 2] A schematic diagram showing light scattering from the ophthalmic lens shown in FIG. 1B. [Figure 3A] A cross-sectional view of an exemplary dot composed of a depression on the lens surface. [Figure 3B] A cross-sectional view of an exemplary dot composed of a protrusion on the lens surface. [Figure 3C] A cross-sectional view of another exemplary dot composed of a depression on the lens surface. [Figure 3D] A cross-sectional view of a further exemplary dot composed of a depression on the lens surface. [Figure 4A] A plan view of an exemplary dot peripheral path. [Figure 4B] A plan view of an exemplary dot peripheral path. [Figure 4C] A plan view of an exemplary dot peripheral path. [Figure 4D] A plan view of an exemplary dot peripheral path. [Figure 4E] A plan view of an exemplary dot peripheral path. [Figure 4F] A plan view of an exemplary dot peripheral path. [Figure 4G] A plan view of an exemplary dot peripheral path. [Figure 4H] A plan view of an exemplary dot peripheral path. [Figure 4I] A plan view of an exemplary dot peripheral path. [Figure 4J] This is a plan view of an example of a path around a dot. [Figure 4K] This is a plan view of an example of a path around a dot. [Figure 4L] This is a plan view of an example of a path around a dot. [Figure 4M] This is a plan view of an example of a path around a dot. [Figure 4N] This is a plan view of an example of a path around a dot. [Figure 4O] This is a plan view of an example of a path around a dot. [Figure 4P] This is a plan view of an example of a path around a dot. [Figure 4Q] This is a plan view of an example of a path around a dot. [Figure 4R] This is a plan view of an example of a path around a dot. [Figure 4S] This is a plan view of an example of a path around a dot. [Figure 5A] This plot compares the number of light rays hitting the retina for five different simulated dot shapes. [Figure 5B] This plot compares the number of backscattered rays for five different simulated dot shapes. [Figure 6] This is a schematic diagram of an exemplary laser system for forming dots on the surface of a lens. [Figure 7] This is a plan view of an exemplary laser exposure path for forming dots. [Figure 8] This is a plan view of another exemplary laser exposure path for forming a dot. [Figure 9A] Figure 8 is a top view of an image of two dots formed using the path shown. [Figure 9B] This is the cross-sectional profile of one of the dots shown in Figure 9A. [Figure 10A] Figure 7 is a top view of an image of two dots formed using the path shown. [Figure 10B]This is the cross-sectional profile of one of the dots shown in Figure 10A. [Figure 11A] This is a plan view of an exemplary laser exposure path for forming dots by discrete pulses of laser radiation along the path. [Figure 11B] This is a top view of the image of two dots formed using the path shown in Figure 11A. [Figure 11C] This is the cross-sectional profile of one of the dots shown in Figure 11B. [Figure 12A] This figure shows an exemplary dot pattern on an ophthalmic lens with dots generated by laser burn-in. [Figure 12B] This is a partial enlarged view of the dot pattern in Figure 12A. [Figure 12C] This is an enlarged cross-sectional view of the dots taken at CC in Figure 12B. [Figure 13] This is a flowchart of a method for forming dots using a laser system with laser burn-in for trench formation. [Figure 14] This figure shows an exemplary dot pattern with dots of different sizes. [Figure 15] This figure shows another exemplary dot pattern with dots of different sizes. [Figure 16] This figure shows a further exemplary dot pattern with dots of different sizes. [Figure 17] This figure shows an exemplary dot pattern with overlapping dots. [Figure 18] This figure shows an exemplary dot pattern with overlapping rows of dots. [Figure 19] This figure shows another exemplary dot pattern with rows and columns of overlapping and non-overlapping dots. [Figure 20] This figure shows another exemplary dot pattern with a radial array of overlapping dots of varying sizes. [Figure 21] This figure shows another exemplary dot pattern with a radial array of overlapping and non-overlapping dots of varying sizes. [Figure 22] This figure shows another exemplary dot pattern with overlapping and non-overlapping dots of varying sizes. [Modes for carrying out the invention]

[0015] In drawings, similar reference numerals indicate similar elements.

[0016] Referring to Figures 1A to 1C, eyeglasses 100 for reducing the progression of myopia are shown. Eyeglasses 100 treat both eyes simultaneously without substantially impairing the wearer's clear vision on the axis. Moreover, these eyeglasses are sturdy and inconspicuous enough to allow the wearer to engage in the same daily activities without the eyeglasses breaking or being concerned about their appearance, which is particularly desirable since these eyeglasses are typically used to suppress elongation of the eyeballs in children.

[0017] The eyeglasses 100 consist of a pair of frames 101 and ophthalmic lenses 110a and 110b fitted within the frames 101. Generally, the ophthalmic lenses can be plano lenses, monofocal lenses (e.g., with positive or negative power) or multifocal lenses (e.g., bifocal lenses or progressive multifocal lenses). The ophthalmic lenses 110a and 110b each have clear apertures 120a and 120b, respectively, which are surrounded by contrast reduction areas 130a and 130b, respectively. The clear apertures 120a and 120b can be positioned to match the wearer's distance visual acuity, with the contrast reduction areas 130a and 130b corresponding to the wearer's peripheral vision and the wearer's line of sight corresponding to distance visual acuity. Lens 110a is shown as pre-edged in Figure 1B.

[0018] Generally, the size and shape of the clear apertures 120a and 120b can vary. Generally, the clear aperture provides the wearer with a visual cone (e.g., 20 / 15 or 20 / 20) in which the wearer's vision can be optimally corrected. In some examples, the aperture has a maximum dimension ranging from about 0.2 mm (e.g., about 0.3 mm or more, about 0.4 mm or more, about 0.5 mm or more, about 0.6 mm or more, about 0.7 mm or more, about 0.8 mm or more, about 0.9 mm or more) to about 1.5 cm (e.g., about 1.4 cm or less, about 1.3 cm or less, about 1.2 cm or less, about 1.1 cm or less, about 1 cm or less). If the aperture is circular (e.g., as depicted in Figures 1A and 1B), this dimension is the diameter D of the circle. 120 It supports circular apertures, but non-circular (e.g., elliptical, polygonal, teardrop-shaped) apertures are also possible.

[0019] A clear aperture can form a solid angle of approximately 30 degrees or less in the viewer's field of view (for example, 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). The solid angles formed in the horizontal and vertical field of view planes may be the same or different.

[0020] In some cases, lenses 110a and 110b may not include a clear aperture, and the contrast reduction area occupies the entire axial field of view.

[0021] Referring to Figure 1B, the contrast reduction area 130a extends to a radius smaller than the pre-edged lens radius and occupies an annular area surrounding the clear aperture 120a. Generally, the contrast reduction area of ​​a pre-edged lens extends far enough after the lens has been edged and fitted into the frame 101 that the desired level of light scattering is achieved with respect to the user's peripheral vision, regardless of the viewing direction while the user is wearing the glasses. The contrast reduction area 130a has a maximum dimension (for example, diameter D in the case of a circular area) in the range of approximately 3 cm to approximately 9 cm (e.g., more than approximately 4 cm, more than approximately 5 cm, more than approximately 6 cm, more than approximately 7 cm, for example, less than or equal to approximately 8 cm). 130 ) can have a circular perimeter. The contrast reduction area 130a has a circular perimeter, but other shapes are also possible (e.g., elliptical, polygonal, etc.).

[0022] Referring particularly to Figure 1C, the contrast reduction areas 130a and 130b contain scattering centers (also referred to as “dots” 112) that reduce the contrast of objects in the wearer’s peripheral vision by scattering light that passes through those areas and reaches the wearer’s eye. The lens area 140 between the dots corresponds to the original (e.g., Rx) lens surface that provides the wearer with a clear, focused image. The result of the contrast reduction areas 130 is that the wearer is provided with a high-resolution image that corrects any refractive errors in the wearer, with a reduced contrast level compared to the on-axial image seen through the clear apertures 120a and 120b.

[0023] Generally, the contrast reduction area of ​​a lens may consist of hundreds or thousands of dots, the dimensions of which may be the same across each lens or may vary. For example, the dimensions may increase or decrease as a function of the location of the dot (e.g., when measured from a clear aperture) and / or as a function of the distance from the edge of the lens. In some examples, the dimensions of the dots change monotonically as the distance from the center of the lens increases (e.g., monotonically increasing or decreasing). In some cases, the monotonic increase / decrease of dimensions involves linearly changing the diameter of the projection as a function of the distance from the center of the lens.

[0024] The dots shown in Figure 1C are irregularly arranged on the lens surface. Generally, the dots are arranged so that they collectively provide sufficient contrast reduction for myopia reduction around the viewer. Typically, smaller dot spacing results in greater contrast reduction. Generally, the dots can be spaced apart from each other or they can overlap. For dots placed at intervals, the distance between adjacent dots can range from 0.05 mm (for example, approximately 0.1 mm or more, approximately 0.15 mm or more, approximately 0.2 mm or more, approximately 0.25 mm or more, approximately 0.3 mm or more, approximately 0.35 mm or more, approximately 0.4 mm or more, approximately 0.45 mm or more, approximately 0.5 mm or more, approximately 0.55 mm or more, approximately 0.6 mm or more, approximately 0.65 mm or more, approximately 0.7 mm or more, approximately 0.75 mm or more) to approximately 2 mm (for example, approximately 1.9 mm or less, approximately 1.8 mm or less, approximately 1.7 mm or less, approximately 1.6 mm or less, approximately 1.5 mm or less, approximately 1.4 mm or less, approximately 1.3 mm or less, approximately 1.2 mm or less, approximately 1.1 mm or less, approximately 1 mm or less, approximately 0.9 mm or less, approximately 0.8 mm or less).

[0025] In general, the coverage of a lens by dots can be varied as desired. Here, coverage refers to the proportion of the total lens area when projected onto the xy-plane, corresponding to the dots. Typically, lower dot coverage will produce less scattering than higher dot coverage (assuming that the individual dots are discrete, i.e., dots do not merge to form larger dots). Dot coverage can vary from over 10% to approximately 75%. For example, dot coverage can be over 15%, over 20%, over 25%, over 30%, over 35%, over 40%, over 45%, for example, 50% or 55%. Dot coverage can be selected according to the user's comfort level, for example, to provide a level of peripheral vision that is comfortable enough for the wearer to voluntarily wear the glasses for extended periods (e.g., all day).

[0026] It is conceivable that light from the scene incident on the lens in the contrast reduction areas 130a and 130b between the dots contributes to the image of the scene on the user's retina, while light from the scene incident on the dots does not. Furthermore, the light incident on the dots is still transmitted to the retina, and therefore, the contrast reduction areas 130a and 130b have the effect of reducing image contrast without substantially reducing the light intensity on the retina. Thus, it is conceivable that the amount of contrast reduction in the user's peripheral vision is correlated (for example, roughly proportional) to the proportion of the surface area of ​​the contrast reduction area covered by the dots. Generally, the dots occupy at least 10% (for example, 20% or more, 30% or more, 40% or more, 50% or more, for example, 90% or less, 80% or less, 70% or less, 60% or less) of the area of ​​the contrast reduction areas 130a and 130b (when measured in the xy plane).

[0027] Generally, dot patterns reduce the contrast of object images in the wearer's peripheral vision without significantly worsening the viewer's visual acuity in this area. Here, peripheral vision refers to the field of view outside the field of clear aperture. Image contrast in these areas can be reduced by more than 40% (e.g., more than 45%, more than 50%, more than 60%, more than 70%, more than 80%) compared to the image contrast seen using the clear aperture of the lens as determined. Contrast reduction can be set according to the needs of each individual case. Typical contrast reduction is thought to be in the range of approximately 50% to 55%. For very mild cases, a contrast reduction lower than 50% may be used, while on the other hand, more susceptible subjects may require a contrast reduction higher than 55%. Peripheral visual acuity can be corrected to more than 20 / 30 (e.g., more than 20 / 25, more than 20 / 20) as determined by subjective refraction, while still achieving significant contrast reduction.

[0028] Here, contrast refers to the difference in brightness between two objects within the same field of view. Therefore, contrast reduction refers to a change in this difference.

[0029] Contrast and contrast reduction can be measured in various ways. In some embodiments, contrast can be measured based on the difference in brightness between different parts of a standard pattern (e.g., a black and white square checkerboard) acquired through the clear aperture and dot pattern of the lens under controlled conditions.

[0030] 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). With respect to the OTF, contrast is specified with respect to the transmittance of stimuli in which light and dark regions are sinusoidally modulated at different "spatial frequencies". These stimuli appear as bars in which light and dark alternate, and the spacing between the bars varies over a given range. For all optical systems, the transmittance of contrast is lowest for sinusoidally changing stimuli with the highest spatial frequency. The relationship that describes the transmittance of contrast for all spatial frequencies is the OTF. The OTF can be obtained by taking the Fourier transform of the point distribution function. The point distribution function can be obtained by imaging a point light source onto a detector array through the lens and by determining how light from the point is distributed across the detectors.

[0031] When measurement results are inconsistent, OTF is a suitable technique.

[0032] 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. This approximation assumes that all light hitting the dots is uniformly distributed across the entire retinal area, which reduces the amount of light available in brighter areas of the image, and this adds light to darker areas. Thus, contrast reduction can be calculated based on light transmittance measurements performed through the clear aperture and dot pattern of the lens.

[0033] Furthermore, contrast can be clinically measured by measuring the change in performance of an observer wearing the lenses with respect to visual acuity (e.g., Snellen or ETDRS letter charts) and / or contrast sensitivity tests (e.g., Pelli-Robbon charts). The change in contrast can be less than one line of visual acuity (i.e., five letters) and can be approximately 0.5 lines, 1 line, 2 lines, or 3 lines or more. It can also be measured in LogMAR units less than 0.05, or approximately 0.05, 0.10, 0.20, or 0.30 or more.

[0034] As previously mentioned, the size, spacing, and arrangement of a dot pattern can generally be varied. In some embodiments, the dot pattern may feature, for example, a gradient in dot size and / or spacing. The dot pattern may also feature a gradient in the scattering efficiency of the dots (for example, due to a gradient in refractive index mismatch and / or shape of each dot). A gradient dot pattern can reduce the visibility of the pattern. For example, a gradient transition from the clear portion to the scattering portion of a lens can be less noticeable than a steep transition.

[0035] Lenses 110a and 110b can be formed from stock lenses. Lenses can be formed from conventional ophthalmic lens materials (e.g., polycarbonate or Tribex®). Lenses can include one or more coatings or other surface treatments, including, for example, hard coats, photochromic coatings, blue filters, and anti-reflective coatings.

[0036] Generally, ophthalmic lenses 110a and 110b can be clear or lightly tinted. That is, the lens can be optically transparent to all visible wavelengths and appear clear and / or colorless, or it can contain a spectral filter and appear tinted. For example, an ophthalmic lens can contain a filter that reduces the amount of red light transmitted to the wearer. It is conceivable that excessive stimulation of the L cones in a person's (especially a child's) eye can result in suboptimal elongation and myopia. Therefore, spectrally filtering red light using an ophthalmic lens can further reduce the wearer's myopia.

[0037] Generally, the dots 112 can be provided as protrusions and / or recesses on one or both surfaces of each lens, and / or as scattering inclusions within the lens material itself. In some examples, the dots can be formed by an array of protrusions on each surface of the lenses 110a and 110b (e.g., the rear surface or the front surface).

[0038] The protrusions can be formed from an optically transparent material having a refractive index similar to that of the underlying lens (which is 1.60 with respect to polycarbonate (PC)). For example, in embodiments where the lens is formed from polycarbonate, the protrusions can be formed from a polymer having a refractive index similar to that of PC (e.g., a photoactivated polyurethane or epoxy-based plastic). In addition to PC, the lens itself can also be made from allyl diglycol carbonate plastic, a urethane-based monomer, or other impact-resistant monomer. Alternatively, the lens can be made from one of the denser, high-refractive-index plastics having a refractive index greater than 1.60. In some embodiments, the lens is made from an optically transparent material having a lower refractive index (e.g., CR39 is 1.50 and Trivex is 1.53).

[0039] Each dot 112 is sized and shaped to scatter light incident on it. Generally, a dot forward scatters part of the incident light and backscatters part of it. The forward-scattered light generally exits the lens through the opposite side from where the light is incident, while the backscattered light scatters away from the lens on the side where the light is incident. This light scattering is illustrated in Figure 2, which shows a lens 110a with scattering centers (e.g., dots 112) on the front surface of the lens. The lens axis 203 is shown for reference and corresponds, for example, to the rotational symmetry axis of the lens, and the lens corrects only spherical aberration.

[0040] Four incident rays 206, 208, 210, and 212 are shown, each incident on a different dot 112. Depending on the angle of incidence of the rays and the shape of the dot, the light can be forward-scattered (rays 214 and 218) and / or backward-scattered (rays 216 and 220). Depending simultaneously on the forward-scattering angle and the wearer's visual axis, forward-scattered light entering the eye 224 can be incident on the wearer's fovea, or away from the wearer's fovea, or directed away from the retina entirely. Generally, scattered light (unlike other light that can be focused by the lens) will not be imaged 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 may be undesirable. Scattered light incident on the retina away from the fovea can reduce the contrast of the wearer's peripheral vision and may reduce the progression of myopia, as previously discussed. This forward-scattered light can be considered "therapeutic light." In some (but not all) cases, other forward-scattered light (for example, whether it is incident on the fovea or on the outer edge of the peripheral visual field of the retina) is not considered therapeutic. Therefore, it may be desirable to forward-scatter the light in a direction that contributes to peripheral visual field contrast reduction but not to foveal contrast reduction. Alternatively, in certain cases, forward-scattered light that contributes to foveal contrast reduction may be acceptable.

[0041] Generally, light scattered into a cone that contributes to the reduction of image contrast in the peripheral field of view is considered to be narrow-angle forward scattering, while light outside this cone is considered to be wide-angle forward scattering. The solid angle (depicted by the outline 222 of a cone with a cone angle 223 in Figure 2) can be useful in distinguishing between wide-angle and narrow-angle scattering. Light scattered within the cone (e.g., ray 218) is narrow-angle forward scattering, while light scattered outside the cone (e.g., ray 214) is wide-angle scattering. The cone angle for narrow-angle scattering can be in the range of 1 to 5 degrees. In some examples, the cone angle for narrow-angle scattering can be 2.5 degrees.

[0042] Some of the incident light rays are scattered backward; for example, incident rays 208 and 212 are scattered backward, becoming the backscattered rays 216 and 220. The backscattered light can be seen by people other than the wearer, making the dots noticeable to those looking at the wearer. Therefore, it may be desirable to reduce (e.g., minimize) the amount of backscattered light while increasing (e.g., maximizing) the amount of forward-scattered light into a narrow angle to a threshold amount of peripheral image contrast reduction sufficient to have the therapeutic effect described above.

[0043] With respect to light incident on a contrast reduction area, the amount of scattered light (which is forward-scattered and / or back-scattered) can be measured using a scanning scattermeter. A scanning scattermeter is an instrument having a light source (e.g., a laser) and a detector (e.g., a single-pixel detector). The sample is illuminated by a collimated beam from the light source, and the detector is scanned on a spherical surface around the sample to generate a map of where the light is going. Using this method, the total amount of light incident on a contrast reduction area that is back-scattered can be less than 12%, less than 10%, less than 9%, less than 8%, less than 7%, less than 6%, less than 5%, less than 4%, less than 3%, less than 2%, or less than 1%. The percentage of backscattered light can be 50% or less, 40% or less, 30% or less, 20% or less, 10% or less, or less than 10%, for example, 9% or less, 8% or less, 7% or less, 6% or less, 5% or less, 4% or less, 3% or less, 2% or less, for example, 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, for example, 99%. The percentage of forward-scattered light scattered in narrow-angle scattering directions (discussed above) can be 50% or more, 60% or more, 70% or more, 80% or more, 90% or more, for example, 95%.

[0044] In some cases, the amount of light that is forward-scattered and / or back-scattered can be determined by optical computer simulation using commercially available optical design software (e.g., Zemax (AnSys) or Code V (Synopsys)). Using this method, the total amount of light incident on the back-scattered contrast reduction area 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 scattered light can be 50% or less, 40% or less, 30% or less, 20% or less, 10% or less, or less than 10%, for example, 9% or less, 8% or less, 7% or less, 6% or less, 5% or less, 4% or less, 3% or less, 2% or less, for example, 1%. The percentage of scattered light that is forward-scattered 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, for example, 99%.

[0045] Therefore, generally, the dot pattern in contrast reduction areas 130a and 130b, as well as the shape of each dot, are selected based on various design parameters to provide the desired degree of light scattering to offer an optimal therapeutic effect while minimizing the amount of backscattered light. Generally, these design parameters include, for example, the dot pattern (i.e., dot density, dot density distribution, relative position of dots, etc.), its size and shape, its refractive index, and other properties (e.g., the transmission and reflection properties of the dots over various wavelengths). Ideally, the dot pattern is selected to provide high visual acuity in the fovea, reduced image contrast in other parts of the retina, and with sufficiently low discomfort to the wearer to allow for prolonged continuous wear. For example, it may be desirable for a child to be able to wear the glasses comfortably for most (if not all) of the day. It is also possible that the dot size, shape, and dot pattern are selected to provide a relatively low amount of backscattered light.

[0046] Examples of dot patterns are described in U.S. Patent Application Publication No. 20190033619A1, titled "Ophthalmic lenses for treating myopia," and U.S. Patent Application Publication No. 20190235279A1, titled "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.

[0047] Various different metrics can be used to evaluate the performance of a dot pattern in order to optimize the dot pattern for use in myopia-reducing eyeglasses. For example, the dot pattern can be empirically optimized based on physical measurements of lenses with different dot patterns. For example, light scattering can be characterized based on haze measurements (e.g., international testing standards for haze (e.g., ASTM D1003 and BS EN ISO 13468)). Conventional haze meters can be used, such as the BYK-Gardner haze meter (e.g., Haze-Gard Plus instrument) which measures how much light is transmitted completely through the lens, the amount of light transmitted undisturbed (e.g., within 0.5 degrees), how much is deflected beyond 2.5 degrees, and clarity (amount within 2.5 degrees). Other instruments can also be used to characterize light scattering for the purpose of empirically optimizing the scattering pattern. For example, instruments that measure light diffusion by measuring light in an annular ring around 2.5 degrees can be used (e.g., instruments from Hornell).

[0048] Alternatively, or additionally, the dot pattern can be optimized using computer modeling software (e.g., Zemax or Code V).

[0049] Alternatively, or additionally, the dot pattern can be empirically optimized by designing various patterns and by measuring forward and backscattering using the methods described above.

[0050] In some examples, the dot shape and dot pattern can be designed based on the optimization of the point distribution function, which is a representation of the image of the scattering centers on the retina. For example, the size, shape, and spacing of the scattering centers can be varied to uniformly spread the illumination of the retina, so that the retina outside the fovea is uniformly covered by scattered light, reducing (e.g., minimizing) the contrast in this region of the retina.

[0051] Alternatively, or additionally, dot shapes and dot patterns can be designed based on the optimization of a 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 of a given range of spatial frequencies. The design parameters of the dot pattern can be varied to increase or decrease specific spatial frequencies as desired. Generally, 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. Dot patterns can be designed to provide an amplified signal in a specific subset of spatial frequencies within this range.

[0052] As described above, dots can be provided on one or both surfaces of a lens, or within the lens itself. With respect to dots formed on a lens surface, dots can be formed as projections from the lens surface or as depressions in the surface. Examples of depressions and projections are shown in Figures 3A and 3B, respectively. In Figure 3A, dot 301 is formed as a depression in the lens surface 310. In the cross-sectional profile, the shape of dot 301 is characterized by a width or lateral dimension W and a depth D. 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. Depth refers to the vertical dimension of the dot measured from the edge of the dot to the base of the dot. Here, the depression has a parabolic profile, which is symmetrical about a central vertical axis corresponding 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 (for example, in the case of a dot with a circular circumference), or it can vary for each different cross-section. Examples of dot surrounding shapes are discussed below.

[0053] Generally, the width, depth, and shape can be varied as desired. Furthermore, as discussed below, the width and depth can affect how much light the dot scatters. In some examples, the dots have widths ranging from 10 μm to 2,000 μm (for example, the maximum width if the width varies depending on the cross-section), such as 50 μm or more, 100 μm or more, 150 μm or more, 200 μm or more, 250 μm or more, 300 μm or more, 350 μm or more, 400 μm or more, 450 μm or more, 500 μm or more, 600 μm or more, 700 μm or more, 800 μm or more, 900 μm or more, and 1,750 μm or less, 1,500 μm or less, 1,250 μm or less, 1,000 μm or less, 900 μm or less, 800 μm or less, 700 μm or less, 600 μm or less, 500 μm or less, etc., for example, in the range of 100 μm to 400 μm, in the range of 200 μm to 350 μm, etc. Dot 301 is (for example, 5 μm or more, 10 μm or more, 20 μm or more, 30 μm or more, 40 μm or more, 50 μm or more, 60 μm or more, 70 μm or more, 80 μm or more, 90 μm or more, 100 μm or more, 110 μm or more, 120 μm or more, 130 μm or more, 140 μm or more, 150 μm or more, 175 μm or more, 200 μm or more, and for example, 450 μm or less, 400 μm or less, 35 It is possible to have depths ranging from 2 μm to 500 μm, such as 0 μm or less, 300 μm or less, 250 μm or less, 200 μm or less, 150 μm or less, 120 μm or less, 100 μm or less, 50 μm or less, 30 μm or less, 20 μm or less, for example, in the range of 10 μm to 150 μm, for example, in the range of 20 μm to 100 μm, for example, in the range of 30 μm to 80 μm.

[0054] The depth of the depression can be smaller than its width. For example, the ratio D / W can be in the range of 1 / 50 to 9 / 10 (e.g., 1 / 40 or more, 1 / 30 or more, 1 / 20 or more, 1 / 10 or more, 1 / 5 or more, 1 / 4 or more, 1 / 3 or more, 1 / 2 or more, and for example, 4 / 5 or less, 7 / 10 or less, 3 / 5 or less, 1 / 2 or less, 1 / 3 or less, 1 / 4 or less, etc.).

[0055] In certain cases, the depth is 20 μm or less, and the width (e.g., maximum width) is 100 μm or more.

[0056] It is conceivable that dots with a depth smaller than their width (e.g., D / W as described above) may have reduced backscattering compared to dots with a depth equal to or greater than their width. Reduced backscattering can generally be associated with shallower dots (e.g., dots with a depth of 50 μm or less). While we do not wish to be constrained by theory, reduced backscattering may be due to fewer ray paths, including multiple reflections, which are more likely to occur as the depth or aspect ratio of the dot increases.

[0057] Figure 3B shows a dot formed as a projection 302 having a width W and a height (e.g., maximum height) H. The width range for the projection 302 can be the same as that for the depression of the dot 301. The height range can be the same as the depth range for the depression of the dot 301. Similar to the depression of the dot 301, a higher aspect ratio H / W for the projection 302 results in a higher rate of backscattering as opposed to forward scattering.

[0058] The profiles of dots 132 and 134 are parabolic in the cross-sections shown in Figures 3A and 3B, respectively, but the dots can have other profile shapes. For example, in some cases, the dots are crater-shaped, having a central depression extending to a predetermined depth below the lens surface, surrounded by a rim 316 extending to a predetermined height above the lens surface. An example of a crater-shaped dot 303 is shown in Figure 3C. The dot 303 has a width W and depth D as defined above. In addition, the depression 313 has a width WD that is smaller than the overall width W of the dot 303. The rim 316 has a height (e.g., maximum height if the height varies around the periphery) HR and a width (e.g., maximum width if the width varies around the periphery) WR. W and D can be within the ranges described above. The WD can be 1,500 μm or less (for example, 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 for example, 50 μm or more, 75 μm or more, 100 μm or more, 120 μm or more, 150 μm or more, 200 μm or more, etc.).

[0059] HR can be smaller than D. For example, HR can be D / 2 or less (e.g., D / 3 or less, D / 4 or less, D / 5 or less, D / 6 or less, D / 8 or less, D / 10 or less). In some cases, HR is 20 μm or less (e.g., 15 μm or less, 12 μm or less, 10 μm or less, 8 μm or less, 5 μm or less, 3 μm or less, 2 μm or less).

[0060] The WR can be 20 μm or less (for example, 15 μm or less, 12 μm or less, 10 μm or less, 8 μm or less, 5 μm or less, 3 μm or less, 2 μm or less).

[0061] The dots can have irregular surfaces. An example of a dot in the form of a crater 304 with an irregular surface is shown in Figure 3D. Here, the crater 304 has a depth D and width W as defined above. The rim 317 has a height HR and width as described above. In addition, the central depression 314 features side walls 318a and 318b as well as a floor 319. The floor 319 extends over a width WF and features an irregular surface with a height variation dF. Here, WF is measured from the base of one side wall 318a to the base of the opposite side wall 318b. The base of the side walls can be identified as the smallest local location in the cross-sectional surface profile of the depression (where the height of the floor begins to increase).

[0062] When the sidewall is vertical, WD = WF. Typically, WD will be equal to 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 cases, WF is 500μm or less (e.g., 400μm or less, 300μm or less, 250μm or less, 200μm or less, 150μm or less, 100μm or less, 80μm or less, e.g., approximately 20μm or more, 50μm or more, 75μm or more, 100μm or more, etc.).

[0063] In some cases, small values ​​with respect to dF correspond to a smooth and flat floor 319. For example, dF can be less than or equal to 0.5D (e.g., less than or equal to 0.4D, less than or equal to 0.3D, less than or equal to 0.2D, less than or equal to 0.15D, less than or equal to 0.1D, less than or equal to 0.075D, less than or equal to 0.05D). dF can be less than or equal to 50μm (e.g., less than or equal to 40μm, less than or equal to 30μm, less than or equal to 20μm, less than or equal to 10μm, less than or equal to 5μm, less than or equal to 3μm, less than or equal to 2μm, for example, greater than or equal to 1μm, greater than or equal to 2μm, greater than or equal to 3μm, greater than or equal to 5μm, greater than or equal to 8μm, greater than or equal to 10μm, etc.).

[0064] In some cases, WF is 0.5W or higher, and dF is 0.2D or lower.

[0065] While we do not wish to be constrained by theory, it is conceivable that dots with relatively steep sidewalls (e.g., WD is not significantly greater than WF) (i.e., relatively shallow (e.g., D is 50 mm or less)) and relatively flat floors (e.g., dF is 0.2 D or less) can have a relatively low amount of backscattered light and, preferably, can forward scatter light into a relatively narrow angle. Therefore, such dots can provide lenses with reduced visibility and high therapeutic efficacy.

[0066] In general, the shape of dots formed on a lens surface, such as those described above, can be determined using conventional surface measurement techniques (e.g., SEM microscopy, optical interferometry, etc.) and conventional image analysis techniques to extract dimensions from images obtained using these measurement techniques.

[0067] As previously mentioned, the dot shape for a surface dot is defined by the surrounding shape in addition to the cross-sectional profile. Generally, dots can be formed with any surrounding shape depending on the resolution of the method used to form the dot. Generally, when dots are formed using a method that involves depositing, removing, or modifying material on the surface of a lens, it is possible to form dots by scanning a dotting apparatus (e.g., a laser (an example discussed below)) along a path, modifying the lens surface at that location, and tracing and drawing the dot shape onto the lens surface. Various path shapes for forming different dot perimeters are shown in Figures 4A to 4S. Depending on the resolution of the dotting apparatus and the size of the dot (e.g., width, as discussed previously), the dotting apparatus can be scanned along multiple paths, one into the other, to modify the lens surface of the entire dot.

[0068] In the first example in Figure 4A, the dot 401 has a star-like shape with five points. The dot is formed by scanning the device along the paths 401a of the first star shape and 401b of the second star shape, forming inside path 401a and concentrically with path 401b. Each of paths 401a and 401b can correspond to a rim as described with respect to Figure 3D.

[0069] Figure 4B shows pear-shaped dots 402 formed by tracing a dot-forming device along a first path 402a and a second path 402b within the first path 402a. The shapes of the first and second paths 402a and 402b can be substantially the same, with the second path 402b being smaller in size. Each of paths 402a and 402b includes regions with sharp turns and smooth turns.

[0070] Figure 4C shows a generally trapezoidal dot 403 formed by a single path 403a. Path 403a contains relatively small segments compared to the rest of the segments forming the trapezoidal shape on the upper side of path 403a.

[0071] Figure 4D shows the dot 404 path formed by tracing the lens forming apparatus along two elliptical paths 404a and two straight lines 404b. Path 404a is smooth and curved, while lines 404b are straight.

[0072] Figure 4E shows an example of an octagonal dot 405 formed by scanning a dot-forming device along a continuous segmented spiral path 405a. Since the beam following the path 405a has a finite width, the resulting dots 405 can be depressions in other parts of the path 405a with irregular depths.

[0073] Figure 4F shows another example of polygonal dots formed by scanning a dot-forming device along a continuous segmented spiral path 406a. Compared to path 405a, path 406a contains fewer linear segments, and the outline of dot 406 differs from that of dot 405.

[0074] Figure 4G shows an example of an approximately circular dot 407 formed by scanning a dot-forming device along a continuous helical path 407a. Path 407a is smoother compared to paths 405a and 406a.

[0075] Figure 4H shows dumbbell-shaped dots 408 formed by tracing a dot-forming device 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 (e.g., aspect ratio).

[0076] Figure 4I shows trapezoidal dots 409 formed by tracing the dot forming apparatus along the first path 409a and the second path 409b within the first path 409a. Each of paths 409a and 409b is similar to path 403a.

[0077] Figure 4J shows crescent-shaped dots 410 formed by tracing the dot-forming apparatus along a first path 410a and a second path 410b within the first path 410a. Because path 410a is relatively narrow (for example, has a high aspect ratio), path 410b can be much shorter than path 410a, while still maintaining a relatively flat floor.

[0078] Figure 4K shows a zigzag-shaped dot 411 formed by tracing a dot-forming device along a single closed path 411a. The path 411a typically includes linear segments that meet at various angles.

[0079] Figure 4L shows a cat's head shaped dot 412 formed by tracing the dot-forming apparatus along a first path 412a and a second path 412b within the first path 412a. By having the beam follow path 412b within path 412a, the overall depth profile within the dot 412 can be more consistent compared to, for example, following only path 412a.

[0080] Figure 4M shows another crescent-shaped dot 413 formed by tracing the dot-forming apparatus along the first path 413a and the second path 413b within the first path 413a. Compared to the crescent-shaped dot 410, the aspect ratio of dot 413 is lower, and therefore the first and second paths 413a and 413b are closer in size to paths 410a and 410b.

[0081] Figure 4N shows a cone-shaped dot 414 formed by tracing the dot-forming apparatus along a first path 414a and a second path 414b within the first path 414a. Both paths 414a and 414b consist of slightly curved segments.

[0082] Figure 4O shows polygonal dots 415 formed by tracing a dot-forming apparatus along a series of hexagonal paths 415a (e.g., a honeycomb grid). The beam can follow various routes to form paths 415a.

[0083] Figure 4P shows circular dots 416 formed by tracing a dot-forming device along a first path 416a and a second path 416b within the first path 416a. Both paths 416a and 416b are circular and concentric.

[0084] Figure 4Q shows an elliptical dot 417 formed by tracing the dot forming device along a first path 417a and a second path 417b within the first path 417a. Both paths are elliptical and concentric.

[0085] Figure 4R shows a rectangular dot 418 formed by tracing the dot forming device along a first path 418a and a second path 418b within the first path 418a. Both paths are rectangular and concentric.

[0086] Figure 4S shows square dots 419 formed by tracing the dot-forming apparatus along a first path 419a, along a second path 419b within the first path 419a, and along a third path 419c within the second path 419b. Each path is square. Since the widths of paths 419a and 419b are relatively large compared to the width of the beams that follow those paths, an additional path 419c exists to ensure a relatively smooth floor.

[0087] Generally, any number of closed paths can be scanned sequentially to form dots of a desired shape, size, and floor. Other shapes are also possible. Shapes that can be formed by scanning the dotting apparatus along a single continuous path may be advantageous because they can be formed more efficiently (e.g., more quickly) than shapes formed by multiple separate paths. This is because a single continuous path typically avoids the need to reset the dotting apparatus by moving it from one path to another.

[0088] The effects of dot size and shape on scattered light can be empirically studied by physical light scattering experiments and / or by optical computer simulations. Optical simulation software was used to model the forward and backscattering properties of scatterers with simple geometric shapes. For the purpose of the simulation, a spectacle lens with the dimensions of a plano lens (124 mm front radius, 123.2 mm rear radius, 2 mm thickness) and a model eye with the same dimensions as a human eye were modeled. Three fields of view at 0, 20, and 40 degrees (full field of view) were used in the model to consider central vision, near-peripheral vision, and mid / far-peripheral vision. In each case, all dots were modeled on the rear surface of the lens (i.e., the surface facing the wearer).

[0089] The results of these simulations are shown in the plots in Figures 5A and 5B. Here, Figure 5A shows the number of simulated rays hitting the wearer's retina for five different dots. Figure 5B shows the number of simulated rays backscattered for the same five different dots. In each plot, the x-axis is the height or depth of the dot, depending on whether the dot is a protrusion or a depression.

[0090] Lines 501a and 501b correspond to dots formed from hemispherical protrusions. Increasing the height of these protrusions did not significantly change the total number of rays hitting the retina, but it did alter the distribution of forward and backscatter.

[0091] Lines 502a and 502b correspond to hemispherical depressions. Ray tracing showed that the hemisphere with the smallest depth (10 μm) provided the greatest forward scattering to the retina and the least backscatter. Increasing the depth of the hemisphere reduced the rays hitting the retina and increased backscatter. This analysis showed that the trend was not linear, meaning there was no further reduction in forward scattering at depths of ~50 μm and no further increase in backscattered rays at depths of ~70 μm.

[0092] Lines 503a and 503b correspond to depressions shaped as hemispheres with concave ends. Ray tracing showed that the concave hemisphere with the smallest depth (10 μm) provided the greatest forward scattering to the retina and the least backscatter. Increasing the depth of the hemisphere reduced the number of rays hitting the retina and increased backscatter. The sharpest increase in backscatter occurred between depths of 40 μm and 60 μm, and the sharpest decrease in forward scattering occurred between depths of 10 μm and 30 μm. This analysis showed that there was no further significant reduction in forward scattering at depths of ~50 μm, and no further increase in backscattered rays at depths of ~60 μm.

[0093] Lines 504a and 504b correspond to depressions shaped as elongated hemispheres in the axial direction of the lens. Ray tracing showed that the hemisphere with the smallest Z height (50 μm) provided the greatest forward scattering to the retina and the least backscatter. Increasing the length of the hemisphere in the Z direction reduced the rays hitting the retina and increased backscatter, however, the rate of change was significantly smaller compared to the rate of change found by adjusting the depth of the hemisphere.

[0094] Lines 505a and 505b correspond to depressions shaped as elongated hemispheres with concave ends. Ray tracing showed that the elongated concave hemisphere with the smallest height (50 μm) provided the greatest forward scattering to the retina and the least backscatter. Increasing the length of the concave hemisphere reduced the number of rays hitting the retina. Increasing the length of the concave hemisphere from 50 μm to 170 μm did not significantly change the backscatter, however, there was a sharp increase in backscatter at heights from 170 μm to 240 μm.

[0095] Based on simulations, both the "hemispheric" and "hemispheric with concave end" exhibited the same trend, namely, increasing depth reduced forward scattering and increased backscatter. In both the "hemispheric" and "concave hemisphere," the extension of the scatterer in the Z direction did not significantly affect either forward or backscatter. However, with respect to the bump, a reasonable number of rays hit the retina for all depths, but backscatter was also high. For larger bumps, ray tracing suggests minimal impact on vision because forward scattering is minimal. The 20μm–30μm range found a balance between light scattering and contrast sensitivity with respect to the protrusion.

[0096] In certain cases, the dot can be designed to deliver reduced narrow-angle scattering and increased wide-angle scattering to produce a uniform light distribution over the retina / low-contrast signal while preserving visual acuity through the geometric shape of the scattering center. For example, the dot can be designed to produce significantly wide-angle forward scattering (e.g., greater than 10%, greater than 20%, greater than 30%, greater than 40%, greater than 50%, deflected only by more than 2.5 degrees, etc.). Narrow-angle forward scattering (i.e., within 2.5 degrees) can be kept relatively low (e.g., less than 50%, less than 40%, less than 30%, less than 20%).

[0097] As described above, dots can be formed on or within a lens (for example, a stock lens) by adding material to the lens, by removing material from the lens, and / or by changing the optical properties of the lens material.

[0098] In some cases, 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., bulk material and / or coating material) to generate dots. Generally, lasers can be used to form dots either on the lens surface or within the lens's bulk material. For example, exposure of a lens surface to a laser beam with sufficient energy can generate dots by leaving small depressions and / or roughened patches on the surface. A dot pattern can be formed on the surface by selectively exposing an area of ​​the lens surface to laser radiation. For example, the laser beam can be moved relative to the surface while the beam is pulsed. Relative motion between the beam and the lens surface can be caused by moving the beam while keeping the surface fixed, by moving the surface while keeping the beam fixed, or by moving both the beam and the surface.

[0099] Generally, 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 light and the lens material. For instance, at certain pulse energies, the lens material can melt at the point of exposure, forming a dot. At some pulse energies, dots can be formed by causing the lens material to foam. This can occur at higher energies than lens melting. At some pulse energies, the interaction between the laser light and the lens material can result in a color change in the lens material (e.g., by carbonization). In yet another case, the lens material can be removed from the lens surface by ablation.

[0100] Furthermore, other laser parameters can affect the properties of the dots formed using the laser. These include the laser wavelength, exposure time (e.g., how long each dot location is exposed), and the number of passes (e.g., exposing one area multiple times, with other areas exposed in between), each of which can be selected to achieve the desired surface modification. In addition, the interaction between the laser light and the lens material will depend on the lens material itself. For example, dots made from lens materials with a lower glass transition temperature can be formed using lower pulse energy or fewer pulses compared to dots made from lens materials with a relatively higher glass transition temperature.

[0101] The resolution of the laser beam on the lens surface can be smaller than the desired dot size. For example, the beam resolution (such as that determined from the FWHM of the intensity profile) can be less than or equal to about 50% of the dot dimensions (e.g., less than or equal to about 25%, less than or equal to about 10%, less than or equal to about 5%, less than or equal to about 1%). In some embodiments, the beam may be able to form features having dimensions of less than or equal to 100 μm (e.g., less than or equal to 50 μm, less than or equal to 20 μm, less than or equal to 10 μm, less than or equal to 5 μm). In such cases, the laser can be used to form complex peripheral shapes and / or dots with a maximum width significantly larger than the focused dot size, although doing so requires scanning the laser along the path to form the dot.

[0102] Referring to Figure 6, the laser system 600 for forming a dot on the surface of a lens includes a laser 620, a beam chopper 630, focusing optics 640, a mirror 650, and a stage 670. The laser 620 directs the laser beam toward the mirror 650, the mirror 650 deflects the beam toward the lens 601, and the lens 601 is positioned relative to the mirror 650 by the stage 670. An actuator 660 (e.g., a piezoelectric actuator) is attached to the mirror 650. The stage includes a lens mounting surface 680 that supports the lens 601. The laser system 600 also includes a controller (e.g., a computer controller) that communicates with the laser 620, the beam chopper 630, and the actuator 660.

[0103] The beam chopper 630 and focusing optics 640 are positioned within the beam path. The chopper 630 periodically interrupts the beam so that the lens 601 is exposed to discrete pulses of laser light. The focusing optics 640 (which typically includes one or more optically driven elements (e.g., one or more lenses)) focuses the beam to a sufficiently small spot on the surface of the lens 601 so that the area ablated by the beam on the lens surface corresponds to a desired dot size. The actuator 660 changes the orientation of the mirror 650 relative to the beam, scanning the pulsed beam to different target points on the lens surface. The controller 610 coordinates the operation of the laser 620, chopper 630, and actuator 660 so that the laser system forms a predetermined dot pattern on the lens.

[0104] In some implementations, the stage 670 also includes an actuator. The stage actuator can be a multi-axis actuator, for example, moving the lens in two lateral dimensions perpendicular to the beam propagation direction. Alternatively, or additionally, the actuator can move the stage along the beam direction. Moving the stage along the beam direction can be used to maintain the exposed portion of the lens surface at the beam's focal point, regardless of the curvature of the lens surface, thereby making it possible to maintain a substantially constant dot size across the lens surface. The stage actuator can also be controlled by a controller 610, which links this stage movement with other elements of the system. In some embodiments, the stage actuator is used instead of a mirror actuator.

[0105] Generally, the laser 620 can be any type of laser capable of generating light with sufficient energy to modify a lens material (e.g., bulk lens material or coating) to form dots. The laser can have wavelengths in the UV, visible, or IR portion of the electromagnetic spectrum. Gas lasers, chemical lasers, dye lasers, solid-state lasers, and semiconductor lasers can be used. In some embodiments, infrared lasers (e.g., CO2 lasers (with emission wavelengths at 9.4 μm or 10.6 μm)) can be used. Commercially available laser systems can be used, such as the CO2 laser system from Universal Laser Systems, Inc. (Scottsdale, AZ) (e.g., the 60W VLS 4.60 system). In some implementations, femtosecond lasers can be used. Commercially available femtosecond laser systems can be used, such as those from Trumpf (Santa Clara, CA) (e.g., the TruMicro 2030 laser device in the TruLaser Station 5005), to form dot patterns of desired shape and size. The burst mode of such laser devices can achieve much higher burst energies compared to the maximum energy of a single pulse, leading to a higher ablation rate. This exemplary laser system is capable of providing a pulse duration of less than 400 femtoseconds with a maximum pulse energy of 50 μJ.

[0106] The pulse duration and pulse energy are typically 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 on the surface of the lens 601. For example, the laser 620 heats and melts a portion of the surface of the lens 601 to form a predetermined pattern. This is because laser etching causes the molten material on the lens 601 to expand, resulting in raised marks that form a predetermined dot pattern.

[0107] In certain implementation configurations, the laser 620 uses laser forming to create a predetermined dot pattern on the lens 601. For example, the laser 620 uses laser forming to melt and deposit a polymer material onto the lens 601 at the locations marked by the laser 620, thus forming a predetermined dot pattern.

[0108] In some examples, the laser 620 uses laser marking to form a predetermined dot pattern on the lens 601. For example, the laser marking forms a predetermined dot pattern on the lens 601 by inducing a color change on the lens 601, for example, due to a chemical or physical change in the portion of the lens 601 that forms the predetermined dot pattern. In another example, the laser 620 uses laser marking to carbonize the lens 601 in order to form a predetermined dot pattern on the lens 601.

[0109] In some implementations, the laser 620 uses ablation to form a predetermined dot pattern on the lens 601. For example, the laser 620 is used to ablate (e.g., remove material) the lens 601 by evaporating or sublimating it to form a predetermined dot pattern. After ablation, craters may be formed on the lens 601.

[0110] In some cases, to reduce the visibility of the dot pattern (for example, to reduce backscattering and reflection at the scattering centers due to the ablation craters), the surface of the ablation craters on lens 601 is modified to reduce surface roughness (for example, to produce dots with a large floor dimension relative to the dot size and dots with a small dF relative to the dot depth). Reducing surface roughness can reduce the effect of small-angle light scattering (for example, when the scattering angle is less than 3 degrees). For example, the surface of the ablation craters on lens 601 can be modified by a second pass ablation to melt the rough surface of the ablation craters (for example, by using lower energy ablation). Lower energy ablation can be performed, for example, by defocusing laser 620 (for example, by increasing the beam width of laser 620). In some implementations, continuing to reduce the visibility of the dot pattern involves defocusing laser 620 over multiple iterations. For example, defocusing the laser 620 occurs in several passes (e.g., for each second, third, fourth, etc. ablation pass) and is accompanied by increased defocusing (e.g., increasing the beam width for each pass), which affects the conicality of the crater (e.g., feathering or smoothing the crater rim). In some implementations, reducing the visibility of the dot pattern involves performing multiple overlapping ablations, with one ablation crater being composed of multiple overlapping ablation craters.

[0111] In some implementations, reducing the visibility of the dot pattern involves coating the rear surface of the lens 601 with an anti-reflective layer. In some implementations, the reflective layer is coated on the front surface of the lens. This is particularly beneficial when laser ablation is performed on the rear surface of the lens 601. Generally, the laser 620 has a stronger effect on the coating than on the lens 601 material and therefore affects the conical nature of the craters (e.g., feathering or smoothing of the crater edges).

[0112] Two examples of laser paths for forming dots, each with a width of 140 μm, are shown in Figures 7 and 8, respectively. Figure 7 shows the dot shape formed by scanning two discrete paths 710 and 720. 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.

[0113] Figure 8 shows a segmented helical path 810 of a laser, in the outer portion 810a of the helical path 810, forming the same octagonal shape as the dot shown in Figure 7. The inner portion 810b of the helical path 810 follows a hexagonal shape rotated 60 degrees relative to path 720, and the middle portion 810c of the path connects the inner portion 810b and the outer portion 810a. Here, the dot is formed by tracing the laser along a single continuous path, and therefore it is not necessary to move the laser from one path to the next to complete the formation of the dot. Such dots can be formed more quickly than dots with two or more discrete paths. Moreover, such paths can result in dots with a smoother floor compared to dots of similar size formed by scanning multiple discrete paths.

[0114] This is evident in the comparison of the dots shown in Figures 9A and 9B and Figures 10A and 10B, where Figures 9A and 9B and Figures 10A and 10B correspond to dots formed using the paths shown in Figures 8 and 7, respectively. In particular, Figures 9A and 9B show two dots formed using a helical path as illustrated in Figure 8. The diagram of this dot was obtained using optical interferometry. Figure 9B shows a cross-sectional profile through the cross-section of one of the dots, showing height-vs-location along line 901 in Figure 9A, for example. For example, the dots in Figures 9A and 9B have a maximum height of 1.262 μm above the surface (e.g., 0 μm) and a minimum height of -12.583 μm below the surface, and extend over a range of approximately 14 microns.

[0115] Figure 10A shows a top view of three dots formed using the double path shown in Figure 7. Figure 10B shows the profile through one of the dots (e.g., height-vs-place along line 1001 in Figure 10A), illustrating significantly higher surface roughness at the floor of one of these dots compared to that in Figure 9A. For example, the dots in Figures 10A and 10B have a maximum height of 3.572 μm above the surface (e.g., 0 μm) and a minimum height of -11.427 μm below the surface, and extend over a range of approximately 15 microns, for example.

[0116] These two examples are laser exposures involving continuous exposure of the lens surface while the laser scans each discrete path. However, other exposure schemes are also possible. For example, in some cases, the laser can be pulsed while it is scanned along a discrete path. An example of this is shown in Figure 11A, which shows a helical path 1101. The laser is pulsed as the laser scans along path 1101, resulting in multiple individual exposure areas. The helical path is wound tightly enough relative to the focal size, so that the exposure areas overlap along the path and also overlap with exposure areas in adjacent loops of the helix. The result is an approximately circular dot with a relatively smooth floor. Moreover, such exposure schemes can result in a lower overall laser dose delivered to the area of ​​the lens, resulting in a shallower dot compared to forming a dot by a single continuous exposure.

[0117] An example of dots formed using a helical path and pulsed laser is shown in Figure 11B, which shows top views of three such dots. Figure 11C shows a cross-sectional profile of one of the dots, for example, along line 1103 in Figure 11B, showing height-vs-location. In this example, the maximum height of the dot is 1.466 μm above the surface, and the minimum height is approximately -4.363 μm. The floor roughness through this cross-section is only slightly less than the depth, but the overall floor has relatively small roughness given how shallow the dot is. In other words, the variation dF is not much less than the depth D, but the depth D is very shallow, and the absolute value of dF is small.

[0118] Laser formation of a dot can result in a phenomenon called "burn-in," where the initial exposure location at the start of the laser path results in a deeper portion of the dot compared to the rest of the dot. Such burn-in can manifest as a trench on one side of the dot. The asymmetry resulting from such a burn-in trench can result in asymmetrical scattering from different parts of the dot. In some implementations, for example, when burn-in is unavoidable, it may be desirable to form burn-in trenches symmetrically at different locations within the dot to reduce asymmetrical scattering. Furthermore, the location of the burn-in trenches can be varied across the lens with respect to different dots, either to reduce the overall asymmetry of scattering or to exploit the asymmetry across the entire contrast reduction region of the lens.

[0119] Such an example is illustrated here with reference to Figures 12A–12C. Figure 12A shows a plan view of lens 1200 with a contrast reduction region 1208 surrounding a clear aperture 1212. The contrast reduction region 1208 includes dots 1216 arranged in a radial array pattern. Each dot 1216 includes a depression formed on the surface 1220 of lens 1200 using a symmetric burn-in technique, which results in two trenches on opposite sides of the dot.

[0120] This is illustrated in Figures 12B and 12C, which show a plan view of a portion of the contrast reduction region 1208 and a cross-section through one of the dots, respectively. Each dot 1216 includes a first sidewall 1224, a second sidewall 1228, and a central area 1232 between the sidewalls 1224 and 1228. The depth profile (Figure 12C) shows a depression generated by the burn-in of laser radiation during dot formation, which includes trenches 1236 and 1240 adjacent to the sidewalls 1224 and 1228, respectively.

[0121] The first trench 1236 has a depth D1 that is substantially equal to the depth D2 of the second trench 1240. The central area 1232 located between the first trench 1236 and the second trench 1240 has a depth D3, which is smaller than the depth D1 of the first trench 1236 and the depth D2 of the second trench 1240.

[0122] As used herein, a “trench” may include a groove, channel, cavity, or dimple that is deeper than the depth of the adjacent part. Generally, trenches on opposite sides of a dot may have the same or different depths.

[0123] As shown in Figure 12B, the trench width is not constant around the dots. Rather, each trench is crescent-shaped, with a widest part corresponding to cross-section C and a narrowest part passing through a cross-section perpendicular to C. The orientation of the crescent-shaped trenches is aligned with the radial direction of the dot array within the contrast reduction region 1208. This variation in trench alignment can provide an increase in the overall homogeneity of light scattering averaged across the contrast reduction region.

[0124] The varying depth of the depth profile illustrated in Figure 12C can be formed using laser burn-in in various ways. A first exemplary method 1300 for forming a dot 1216 having a symmetrical depth profile is illustrated in Figure 13. In this method 1300, the laser exposure time at various locations of the dot 1216 is controlled to produce a symmetrical burn-in depression. First, a first step 1304 of method 1300 includes focusing the laser beam of the laser system. A second step 1308 of method 1300 includes exposing a first location of the ophthalmic lens 1200 of the lens material to the focused laser radiation of the laser beam. Specifically, when forming a new dot 1216 within the surface 1220 of the lens 1200, the laser exposes the lens surface 1220 to an initial burst of intense laser radiation, thereby generating an initial burn-in, which defines a first sidewall 1224 and a first trench 1236 positioned inward relative to the first sidewall 1224. In a third step 1312, the method 1300 includes exposing the lens 1200 to focused laser radiation while causing a relative motion between the laser beam and the lens in a first direction M (away from the first trench 1236). In some examples, the laser moves relative to the lens 1200 in the M direction away from the first sidewall 1224, continuing to form the remainder of the dot depression. While the laser moves in direction M, the lens 1200 is continuously exposed to the focused laser radiation of the laser beam, causing it to produce a burn-in that defines the central area 1232 of the dot 1216. The intensity of the laser beam during the formation of the central area 1232 is weaker than the initial burst of laser radiation, and therefore the depth D3 of the central area 1232 is smaller than the depth D1 of the first trench 1236.

[0125] In the fourth step 1316, the method 1300 includes the step of exposing a second location of the ophthalmic lens to focused laser radiation to form a second sidewall portion 1228 and a second trench 1240 positioned inward relative to the second sidewall portion 1228 of the dot 1216. Again, since the intensity of the laser is weaker than the initial burst of radiation, the laser rests for a predetermined period of time, exposing the second trench 1240 to radiation sufficient to produce a burn-in having a depth D2 substantially equal to the depth D1 of the first trench 1236. Thus, the lens 1200 is exposed to the laser beam in the second trench 1240 for a longer period of time than the initial exposure in the first trench 1236.

[0126] In some examples, the intensity of the laser beam is controlled to create symmetrical burn-in depressions. In this example, the laser beam exposes lens 1200 to a first laser intensity to create a first trench 1236, and exposes a different location on lens 1200 to the first laser intensity to create a second trench 1240.

[0127] In some examples, the intensity and exposure time are controlled to produce symmetrical burn-in depressions. In another example, the laser exposure can be pulsed to generate short, intense bursts of laser radiation, forming first and second trenches of the dot before forming the central area.

[0128] In some cases, the dot pattern includes dots that are randomly displaced relative to a regular array. Introducing random displacement can reduce optical effects associated with regularly spaced scattering centers (e.g., glare like starburst). See, for example, https: / / www.slrlounge.com / diffraction-aperture-and-starburst-effects / (which illustrates the starburst effect when it relates to photography). Thus, including random displacement in a dot pattern can provide a more comfortable experience for the user compared to a similar dot pattern where the scattering centers are uniformly spaced. Alternatively, or additionally, randomization of the dot pattern can reduce optical effects that appear in reflected light (e.g., diffraction or interference effects), thereby reducing the visibility of the dot pattern to the observer.

[0129] Referring to Figure 14, the exemplary dot pattern 1400 includes an annular region 1404 surrounding a clear aperture 1408. The annular region has dots 1412 arranged in pattern 1400, including radial B and circumferential C directions. Specifically, the dots 1412 are arranged along multiple radial arrays 1416 relative to the clear aperture 1408, and also within spaces 1420 between 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 within spaces 1420 between radial arrays 1416. According to pattern 1400, the dot size changes when moving in the circumferential C direction, and remains uniform when moving in the radial B direction.

[0130] Furthermore, pattern 1400 includes a second annular region 1424 within the annular region 1404 and adjacent to the aperture 1408, where the dots 1412A are of the 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 three or more annular regions with diverse patterns of dots.

[0131] Figure 15 shows another exemplary dot pattern 1500, which includes an annular region 1504 surrounding a clear aperture 1508. The annular region 1504 has spaced-out dots 1512 arranged in a pattern including radial E and circumferential F directions. Specifically, the dots 1512 are arranged along multiple radial arrays 1516 relative to the aperture 1508 and in the spaces 1520 between different radial arrays 1516. Specifically, dots 1512A of a first size are arranged along the radial arrays 1516, and dots 1512B of a different size are arranged in the spaces 1520 between radial arrays 1516 within the first annular region 1504. According to pattern 1500, when moving in the circumferential direction F, the dot size changes, and when moving in the radial direction E, the dot size remains uniform.

[0132] Furthermore, pattern 1500 includes a second annular region 1524 adjacent to aperture 1508 within the annular region 1504, where the dots 1512A are of the first size. In the second annular region 1524, the dot size is uniform in both the radial direction E and the circumferential direction F2.

[0133] In Figure 16, another exemplary dot pattern 1600 for an ophthalmic lens includes an annular contrast reduction region 1604 surrounding a clear aperture 1608. The annular region 1604 has spaced-out dots 1612 that scatter incident light. The dots 1612 are arranged in a pattern including radial G and circumferential H directions. Specifically, multiple dots 1612 are arranged along multiple radial arrays 1616 relative to the aperture 1608 and in the spaces 1620 between different radial arrays 1616. Dots 1612A of a first size are arranged along the radial arrays 1616, and dots 1612B of a second (smaller) size are arranged in the spaces 1620 between radial arrays 1616 within the first annular contrast reduction region 1604. According to pattern 1600, when moving in the circumferential direction H, the dot size changes, but when moving in the radial direction G, the dot size remains uniform.

[0134] Furthermore, pattern 1600 includes a second annular region 1624 adjacent to aperture 1608, where third-size dots 1612C are arranged between first-size dots 1612A. In the second annular region 1624, the dot size varies in the circumferential direction H2. The third-size dots 1612C are arranged in different patterns, including irregular variations in the spacing between adjacent dots 1612A. In the illustrated example, the third-size dots 1612C are randomly distributed between radial arrays 1616. However, in other examples, third-size dots 1612C (for example, smaller than dots 1612A and 1612B) can be arranged with uniform spacing between adjacent dots 1612A and 1612C. In yet another example, second-size dots 1612B can also be arranged adjacent to dots 1612A and 1612C of other sizes.

[0135] The exemplary dot patterns described with respect to Figures 12A, 14, 15, and 16 each consist of spaced-apart dots, but patterns with overlapping dots are also possible. For example, referring to Figure 17, the exemplary dot pattern 1700 includes an annular contrast reduction region 1704 surrounding a clear aperture 1708 and overlapping dots 1712 for scattering incident light within the annular contrast reduction region 1704. The dots 1712 are arranged in a random pattern 1700 and are of uniform size. In some cases, one dot overlaps with one other dot, and in other cases, one or more other dots overlap. The dots 1712 can simply touch each other or overlap each other to varying degrees (e.g., overlap of about 1% to about 99% in dot surface area). For example, dot overlap, which is determined by the percentage of the area of ​​a dot that overlaps with one or more other dots, can be 5% or more (e.g., 10% or more, 15% or more, 20% or more, 25% or more, 30% or more, 35% or more, 40% or more, 45% or more, 50% or more, 55% or more, 60% or more, 65% or more, 70% or more, 75% or more, 80% or more, 85% or more, 90% or more, or 95% or more).

[0136] Figure 18 shows another exemplary dot pattern 1800, which includes an annular contrast reduction region 1804 surrounding a clear aperture 1808 and overlapping dots 1812 for scattering light within the contrast reduction region. The dot pattern 1800 includes a grid of vertical rows 1814 and columns 1818. In the illustrated example, dots 1812 located 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 either simply touch each other or overlap each other to varying degrees (e.g., overlap of about 1% to about 99% by area).

[0137] In Figure 19, another exemplary dot pattern 1900 includes an annular contrast reduction region 1904 surrounding a clear aperture 1908 and dots 1912 for scattering incident light in the contrast reduction region. The dot pattern 1900 includes a grid of rows 1914 and columns 1918, where dots 1912 located in row 1914 overlap with adjacent dots 1912 in the same row 1914, and dots 1912 located in column 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 1912 do not overlap with adjacent dots 1912 in the same column (e.g., column 1918A). In some rows 1914 and columns 1918 (for example, row 1914B, column 1918B), some dots 1912 overlap with adjacent dots 1912 in both the same column 1918 and the same row 1914. Multiple dots 1912 can either simply touch each other or overlap each other to varying degrees (for example, overlapping by area from about 1% to about 99%).

[0138] In Figure 20, another exemplary dot pattern 2000 for an ophthalmic lens includes a contrast reduction region 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 and second annular regions 2004, 2024. The dot pattern 2000 includes multiple dots arranged both radially and circumferentially with respect to the aperture 2008. Specifically, the multiple dots 2012 are arranged along multiple radial arrays 2016 with respect to the overlapping aperture 2008, and in the spaces 2020 between different radial arrays 2016. Multiple dots 2012A of a first size are arranged along the radial array 2016 in both annular regions 2004, 2024, while multiple dots 2012B of different sizes are arranged 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 aperture 2008, where the dots 2012A are of the first size. In some cases, dots 2012 overlap with adjacent dots of the same and / or different sizes. In some cases, one dot 2012 overlaps with one other dot 2012, and in other cases, it overlaps with two or more other dots 2012. Multiple dots 2012 can simply touch each other or overlap each other to varying degrees (e.g., from about 1% to about 99% overlap). In other cases, the dot 2012 does not overlap with any other dot 2012.

[0139] In another example in Figure 21, the dot pattern 2100 for an ophthalmic lens includes a contrast reduction region 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, 2124. In the first annular region 2104, some of the dots 2112 of varying size overlap with adjacent dots 2112 of the same or different size. In the second annular region 2124, the dots 2112 are of uniform size and do not overlap with adjacent dots 2112. In some cases, dots 2112 overlap with adjacent dots 2112 of the same and / or different size. In some cases, one dot 2112 overlaps with one other dot 2112, and in other cases, it overlaps with two or more other dots 2112. Multiple overlapping dots 2112 can either simply touch each other or overlap each other to varying degrees (for example, from about 1% to about 99% overlap depending on the area).

[0140] Figure 22 illustrates yet another exemplary dot pattern 2200 for an ophthalmic lens, which includes a contrast reduction region comprising 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, 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, while 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 and third annular regions 2204, 2228 overlaps with one other dot 2212, and in other cases, it overlaps with two or more other dots 2212. Multiple overlapping dots 2212 can either merely touch each other or overlap each other to varying degrees (e.g., overlap of about 1% to about 99% by area).

[0141] In some examples, a dot pattern may feature a gradient in dot size and / or spacing. A dot pattern may also feature a gradient in the scattering efficiency of the dots (for example, due to a gradient in refractive index mismatch and / or shape of each dot). A gradient dot pattern can reduce the visibility of the pattern. For example, a gradient transition from the clear portion to the scattering portion of a lens may be less noticeable than a steep transition.

[0142] In addition to the embodiments of the attached claims and the embodiments described above, the following numbered embodiments are also innovative.

[0143] Embodiment 1 is an ophthalmic lens comprising: a lens body having a pair of opposing curved surfaces; and a plurality of discrete light scattering centers located in at least one area of ​​the opposing curved surfaces, each scattering center having a shape at least partially defined by its peripheral shape, maximum depth D, and maximum width W, wherein the ratio D / W is 1 / 5 or less.

[0144] Embodiment 2 is an ophthalmic lens comprising: a lens body having a pair of opposing curved surfaces; and a plurality of discrete light scattering centers located in at least one area 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, where D is 20 micrometers (μm) or less and W is 100 μm or more.

[0145] Embodiment 3 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 located in at least one area of ​​the opposing curved surfaces, each scattering center having a recess having a maximum depth D and a maximum width W, and a minimum width W floor and maximum depth variation δD floor A floor having a plurality of discrete light scattering centers, W floor It is 0.5W or more, and δD floor These are ophthalmic lenses with a diopter of 0.2D or less.

[0146] Embodiment 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 at least one area of ​​the opposing curved surfaces, each scattering center having a shape at least partially defined by a periphery, maximum depth, and maximum width, wherein the periphery is selected from the group consisting of star-shaped, regular polygon, dumbbell, pear-shaped, parallelogram, crescent, conical, and zigzag.

[0147] Embodiment 5 is an ophthalmic lens comprising: a lens body having a pair of opposing curved surfaces; and a plurality of discrete light scattering centers located in at least one area of ​​the opposing curved surfaces, wherein the density and shape of the light scattering centers in the area are selected such that, with respect to light incident on the area of ​​the lens propagating parallel to the lens axis, the ophthalmic lens backscatters less than 12% of the light incident on the area and forwardscatters the other light incident on the area, and more than 50% of the forward-scattered light is forward-scattered into a solid angle of 5 degrees.

[0148] Embodiment 6 is an ophthalmic lens described in any one of the previous embodiments, wherein the area surrounds a clear area lacking a scattering center.

[0149] Embodiment 7 is an ophthalmic lens described in any one of the previous embodiments, wherein the area is an annular area.

[0150] Embodiment 8 is an ophthalmic lens described in any one of the previous embodiments, wherein the light scattering center is formed on a single surface of the ophthalmic lens.

[0151] Embodiment 9 is an ophthalmic lens according to any one of Embodiments 1 to 7, wherein the light scattering center is formed on only a single surface of the ophthalmic lens.

[0152] Embodiment 10 is an ophthalmic lens as described in Embodiment 9, wherein a single surface is a concave surface.

[0153] Embodiment 11 is an ophthalmic lens as described in Embodiment 9, wherein one of its surfaces is a convex surface.

[0154] Embodiment 12 is an ophthalmic lens described in any one of the previous embodiments, wherein each of the scattering centers has the same shape.

[0155] Embodiment 13 is an ophthalmic lens according to any one of Embodiments 1 to 11, wherein at least some of the scattering centers have different shapes.

[0156] Embodiment 14 is an ophthalmic lens described in any one of the previous embodiments, wherein the ophthalmic lens is an eyeglass lens or a contact lens.

[0157] Embodiment 15 is an ophthalmic lens described in any one of the previous embodiments, wherein the ophthalmic lens is a plano lens, a monofocal lens, or a multifocal lens.

[0158] Embodiment 16 is a method comprising the steps of: exposing the surface of an ophthalmic lens to one or more pulses of laser radiation sufficient to generate light scattering centers on the surface; and moving the laser radiation across the surface while exposing the surface, tracing a path on the surface, wherein the path has a helical shape, and the light scattering centers have a maximum width W in the range of 100 micrometers to 1,000 micrometers.

[0159] Embodiment 17 is a method comprising the steps of: exposing the surface of an ophthalmic lens to one or more pulses of laser radiation sufficient to generate a light scattering center on the surface; and moving the laser radiation across the surface while exposing the surface, tracing a path on the surface, wherein the light scattering center has a maximum width W in the range of 100 to 1,000 micrometers and a peripheral shape selected from the group consisting of star-shaped, regular polygonal, dumbbell-shaped, pear-shaped, parallelogram-shaped, crescent-shaped, conical, and zigzag.

[0160] Embodiment 18 is an ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular region surrounding a clear aperture, the annular region having a plurality of light scattering centers within and / or on at least one of the two opposing surfaces, the annular region being sized and shaped to scatter incident light, wherein the first light scattering center of the plurality of light scattering centers overlaps with adjacent light scattering centers.

[0161] Embodiment 19 is an ophthalmic lens as described in Embodiment 18, wherein the light scattering centers are arranged in a pattern including rows, and the first light scattering center and adjacent light scattering centers are arranged in rows.

[0162] Embodiment 20 is an ophthalmic lens as described in Embodiment 19, wherein the light scattering centers are arranged in a pattern including rows.

[0163] Embodiment 21 is an ophthalmic lens as described in Embodiment 20, wherein the second light scattering center overlaps with the third light scattering center in the row.

[0164] Embodiment 22 is an ophthalmic lens according to Embodiment 20 or 21, wherein the first light scattering center overlaps with a different light scattering center, and the first scattering center and the different light scattering centers are arranged in a row.

[0165] Embodiment 23 is an ophthalmic lens as described in Embodiment 18, wherein the first light scattering center is of a first size, and the adjacent light scattering centers are of a second size different from the first size.

[0166] Embodiment 24 is an ophthalmic lens as described in Embodiment 18, wherein the light scattering centers are arranged in a pattern that includes circumferential and radial directions relative to a clear aperture.

[0167] Embodiment 25 is an ophthalmic lens as described in Embodiment 18, wherein the light scattering centers are arranged in a pattern that includes irregular variations in the spacing between adjacent light scattering centers.

[0168] Embodiment 26 is an ophthalmic lens according to any one of Embodiments 18 to 25, wherein the ophthalmic lens includes a second annular region, and the light scattering centers located in the second annular region do not overlap.

[0169] Embodiment 27 is an ophthalmic lens according to Embodiment 18, wherein the lens has a lens axis, and the aperture and annular region are substantially centered on the lens axis.

[0170] Embodiment 28 is an ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular region surrounding a clear aperture, the annular region having a plurality of light scattering centers spaced apart within the lens body and / or on at least one of the two opposing surfaces, the annular region being sized and shaped to scatter incident light, the light scattering centers being arranged in a pattern including circumferential and radial directions with respect 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.

[0171] Embodiment 29 is an ophthalmic lens as described in Embodiment 28, wherein the first size is uniform and the second size is variable.

[0172] Embodiment 30 is an ophthalmic lens according to Embodiment 28, wherein the ophthalmic lens includes a second annular region disposed between a clear aperture and an annular region, and the light scattering centers disposed in the second annular region are uniform in size in both the radial and circumferential directions.

[0173] Embodiment 31 is an ophthalmic lens according to Embodiment 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.

[0174] Embodiment 32 is an ophthalmic lens as described in Embodiment 28, wherein the light scattering center is substantially circular in shape.

[0175] Embodiment 33 is an ophthalmic lens according to Embodiment 28, wherein the lens has a lens axis, and the aperture and annular region are substantially centered on the lens axis.

[0176] Embodiment 34 is an ophthalmic lens as described in Embodiment 28, wherein the lens is an eyeglass lens or a contact lens.

[0177] Embodiment 35 is an ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular region surrounding a clear aperture, the annular region having a plurality of light scattering centers spaced apart within and / or on at least one of the two opposing surfaces, the light scattering centers arranged in a pattern including circumferential and radial directions 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.

[0178] Embodiment 36 is an ophthalmic lens according to Embodiment 35, wherein the ophthalmic lens includes a second annular region disposed between a clear aperture and an annular region, and the light scattering centers disposed in the second annular region are uniform in size in both the radial and circumferential directions.

[0179] Embodiment 37 is an ophthalmic lens according to Embodiment 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.

[0180] Embodiment 38 is an ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular region surrounding a clear aperture, the annular region having a plurality of spaced-apart light scattering centers on at least one of the two opposing surfaces, each light scattering center having a recess on the surface of the annular region, one or more of the light scattering centers having a depth profile relative to the surface, the depth profile having a first trench positioned toward a first sidewall of the recess and a second trench positioned toward a second sidewall of the recess.

[0181] Embodiment 39 is an ophthalmic lens according to Embodiment 38, wherein the depth profile of the recess is symmetrical with respect to at least one plane.

[0182] Embodiment 40 is an ophthalmic lens as described in Embodiment 38, wherein the depth profile of the recess is axially symmetric.

[0183] Embodiment 41 is an ophthalmic lens as described in Embodiment 38, wherein the maximum depth of the first trench is substantially equal to the maximum depth of the second trench.

[0184] Embodiment 42 is an ophthalmic lens according to Embodiment 41, wherein the area between the first trench and the second trench of one or more light scattering centers has a depth different from the maximum depth of the first trench and the maximum depth of the second trench.

[0185] Embodiment 43 is an ophthalmic lens according to Embodiment 38, wherein the orientation of the trench at one of the different light scattering centers varies at different locations in the annular region.

[0186] Embodiment 44 is an ophthalmic lens according to any one of embodiments 38 to 43, wherein one or more light scattering centers have a circular periphery.

[0187] Embodiment 45 is an ophthalmic lens according to any one of Embodiments 38 to 44, wherein the maximum width of the light scattering center is in the range of 100 micrometers (μm) to 1,500 μm.

[0188] Embodiment 46 is an ophthalmic lens according to any one of Embodiments 38 to 45, wherein the radial dimension of the first trench is 0.3W or less, and W is the maximum width of the light scattering center.

[0189] Embodiment 47 is an ophthalmic lens according to any one of Embodiments 38 to 46, wherein the depth profile includes one or more additional trenches between the first trench and the second trench.

[0190] Embodiment 48 is a method comprising the steps of: exposing a first location of an ophthalmic lens of lens material to focused laser radiation of a laser beam to form a first sidewall portion of optically scattering features on the surface of the ophthalmic lens; causing a relative motion between the laser beam and the lens in a first direction away from the first sidewall portion while exposing the lens to focused laser radiation; and exposing a second location of the ophthalmic lens to focused laser radiation to form a second sidewall portion of optically scattering features, wherein the steps of exposing the first and second locations of the lens cause a depression in the lens material, the depression having a depth profile with respect to the surface of the ophthalmic lens, the depth profile including a first trench positioned toward the first sidewall portion and a second trench positioned toward the second sidewall portion of the dot.

[0191] Embodiment 49 is the method according to Embodiment 48, wherein the step of exposing a first location includes exposing a first location of the lens over a first time period, and the step of exposing a second location includes exposing a second location over a second time period that is longer than the first time period.

[0192] Embodiment 50 is a method according to Embodiment 48 or 49, wherein the first and second sidewall portions form a circular, optically scattering feature.

[0193] Embodiment 51 is the method according to any one of Embodiments 48 to 50, wherein the depth of the first trench is substantially equal to the depth of the second trench.

[0194] Embodiment 52 is a method according to any one of Embodiments 48 to 51, wherein the step of causing relative motion is to generate an area between the first trench and the second trench of one or more dots having depths different from the depths of the first trench and the second trench.

[0195] Embodiment 53 is an ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular region surrounding a clear aperture, the annular region having a plurality of light scattering centers within and / or on at least one of the two opposing surfaces, the annular region being sized and shaped to scatter incident light, the diameters of at least some of the plurality of scattering centers being in the range of approximately 1.001 mm to approximately 1.5 mm, and the spacing between dots varying across the annular region.

[0196] Embodiment 54 is an ophthalmic lens according to Embodiment 53, wherein the light scattering centers are arranged in a pattern including circumferential and radial directions with respect to a clear aperture, the light scattering centers arranged along the radial direction have a uniform size, and the scattering centers arranged along the circumferential direction have a variable size.

[0197] Embodiment 55 is an ophthalmic lens according to Embodiment 53, wherein the ophthalmic lens includes a second annular region disposed between a clear aperture and an annular region, and the light scattering centers disposed in the second annular region are uniform in size in both the radial and circumferential directions.

[0198] Embodiment 56 is an ophthalmic lens as described in Embodiment 53, wherein the first light scattering center of a plurality of light scattering centers overlaps with an adjacent light scattering center.

[0199] Embodiment 57 is an ophthalmic lens according to Embodiment 56, wherein the light scattering centers are arranged in a pattern including rows, and the first light scattering center and adjacent light scattering centers are arranged in rows.

[0200] Embodiment 58 is an ophthalmic lens as described in Embodiment 57, wherein the light scattering centers are arranged in a pattern including rows.

[0201] Embodiment 59 is an ophthalmic lens according to Embodiment 53, wherein the light scattering centers are arranged in a pattern that includes irregular variations in the spacing between adjacent scattering centers.

[0202] Embodiment 60 is an ophthalmic lens according to Embodiment 53, wherein each light scattering center includes a recess in one of the surfaces of the ophthalmic lens, and one or more of the light scattering centers have a depth profile with respect to the surface of the ophthalmic lens, the depth profile including a first trench positioned toward a first sidewall of the light scattering center and a second trench positioned toward a second sidewall of the light scattering center.

[0203] Embodiment 61 is an ophthalmic lens according to Embodiment 60, wherein the depth profile of one or more light scattering centers is symmetrical.

[0204] Embodiment 62 is an ophthalmic lens according to Embodiment 60, wherein the depth of the first trench is substantially equal to the depth of the second trench.

[0205] While this specification contains many specific implementation details, these should not be interpreted as limitations on the scope of any disclosure or claimable, but rather as descriptions of features that may be specific to particular examples of a particular disclosure. Furthermore, certain features described herein in the context of separate examples may be implemented in combination in a single example. Conversely, various features described in the context of a single example may also be implemented separately or in any suitable subcombination in multiple examples. Moreover, features are described herein to act in a particular combination, and may even be initially claimed as such, but one or more features from a claimed combination may, in some cases, be removed from the combination, and the claimed combination may be directed towards a subcombination or a variation of a subcombination.

[0206] Similarly, while operations are depicted in a specific order in the drawings, this should not be understood as requiring that such operations be performed in a specific or sequential order shown, or that all illustrated operations be performed, in order to achieve the desired result. In certain situations, multitasking and parallel processing may be advantageous. Furthermore, the separation of various system modules and components in the examples described herein should not be understood as requiring such separation in all examples, and it should be understood that the described program components and systems can generally be integrated into a single product or packaged into multiple products.

[0207] Specific examples of the subject matter have been described. Other examples are found within the claims below. For example, the actions described in the claims can be performed in a different order, and the desired results can still be achieved. As one example, the process depicted in the attached diagram does not necessarily require the specific order or sequential order shown to achieve the desired results. In certain implementations, multitasking and parallel processing may be advantageous. [Explanation of symbols]

[0208] 100 glasses 101 frames 110a, 110b ophthalmic lenses 112 dots 120a, 120b Clear Aperture 130 Contrast Reduction Area Lens area between 140 dots 203 Lens axis 206 Incident ray 208 Incident ray 210 Incident ray 212 Incident ray 214 Ray of light 216 Ray of light 218 Ray of light 220 Rays 222 Cone outline 223 Cone angle 224 Eye 301 dots 302 Protrusion 303 dots 310 Lens surface 313 Indentation 316 Rim 317 Rim 318a, 318b side wall 319th floor 401 dots 401a The path of the first star shape 401b The path of the second star shape 402 Pear-shaped dots 402a First route 402b Second route 403 Generally trapezoidal dots 403a Single route 404 dots 404a Elliptical path 404b line 405 Octagonal dots 405a Continuous segmented spiral path 406 dots 406a Continuous segmented spiral path 407 A roughly circular dot 407a Continuous spiral path 408 Dumbbell-shaped dots 408a First route 408b Second route 409 Trapezoidal dots 409a First route 409b Second route 410 Crescent-shaped dot 410a First route 410b Second route 411 Zigzag-shaped dots 411a Single closed path 412 cat head shaped dots 412a First route 412b Second route 413 Crescent-shaped dot 413a First route 413b Second route 414 Cone-shaped dots 414a First route 414b Second route 415 Polygonal dots 415a A series of hexagonal paths 416 circular dots 416a First route 416b Second route 417 Elliptical dots 417a First route 417b Second route 418 rectangular dots 418a First route 418b Second route 419 square dots 419a First route 419b Second route 419c Third Route 501a, 501b lines 502a, 502b lines 503a, 503b lines 504a, 504b lines 505a, 505b lines 600 Laser Systems 601 Lens 610 Controller 620 lasers 630 Beam Chopper 640 Focused Optics 650 Mirror 660 Actuator 670 stages 680 Lens mounting surface 710 Outer route 720 Inner route 810 Spiral Path 810a outer part Inner part of 810b Middle part of 810c Line 901 Line 1001 Spiral path 1101 Line 1103 Lens 1200 Contrast reduction region 1208 Clear aperture 1212 Dot 1216 Lens surface 1220 First side wall portion 1224 Second side wall portion 1228 Central area 1232 First trench 1236 Second trench 1240 Dot pattern 1400 Annular region 1404 Clear aperture 1408 Dot 1412 Dot 1412A Dot 1412B Radial array 1416 Space 1420 Second annular region 1424 Dot pattern 1500 Annular region 1504 Clear aperture 1508 Dot 1512 Dot 1512A Dot 1512B Radial array 1516 Space 1520 Second annular region 1524 Dot pattern 1600 Contrast reduction region 1604 Clear aperture 1608 Dot 1612 Dot 1612A Dot 1612B Dot 1612C Radial array 1616 Space 1620 1624 The second annular region 1700 Dot pattern 1704 Annular contrast reduction region 1708 Clear aperture 1712 Dot 1800 Dot pattern 1804 Annular contrast reduction region 1808 Clear aperture 1812 Dot 1814 Row 1818 Column 1900 Dot pattern 1904 Annular contrast reduction region 1908 Clear aperture 1912 Dot 1914 Row 1914A Row 1914B Row 1918 Column 1918A Column 1918B Column 2000 Dot pattern 2004 The first annular region 2008 Clear aperture 2012 Dot 2012A Dot 2012B Dot 2016 Radial array 2020 Space 2024 The second annular region 2100 Dot pattern 2104 The first annular region 2108 Clear aperture 2112 Dot 2124 The second annular region 2200 Dot pattern 2204 The first annular region [ 2208 Clear aperture 2212 Dot 2212A Size 2212B Size 2212C Size 2224 Second ring region 2228 Third ring region B Radial direction C Circumferential direction C2 circumferential direction dF Height fluctuation D Depth D1 Depth of the first trench 1236 D2 Second trench, depth 1240 D3 Central area 1232 depth D 120 diameter D 130 diameter E Radial F Circumferential direction F2 circumferential direction G radial direction H Circumferential direction H2 circumferential direction HR height M First direction W: Width, horizontal dimension WD width WF width WR width

Claims

1. These are ophthalmic lenses, A lens body having a pair of opposing curved surfaces, A plurality of discrete light scattering centers located in at least one area of ​​the opposing curved surfaces, each scattering center having a shape at least partially defined by its periphery, maximum depth D, and maximum width W, An ophthalmic lens having the following features: Ophthalmic lenses with a D / W ratio of 1 / 5 or less.

2. A lens body having a pair of opposing curved surfaces, A plurality of discrete light scattering centers located in at least one area of ​​the opposing curved surfaces, each scattering center having a shape at least partially defined by its periphery, maximum depth D, and maximum width W, An ophthalmic lens having the following features: 、 An ophthalmic lens in which D is 20 micrometers (mm) or less and W is 100 mm or more.

3. A lens body having a pair of opposing curved surfaces that define the lens axis, A plurality of discrete light scattering centers located in at least one area of ​​the opposing curved surfaces, each scattering center having a depression with a maximum depth D and a maximum width W, and a minimum width W ｆｌｏｏｒ and maximum depth variation δD ｆｌｏｏｒ A floor having a plurality of discrete light scattering centers An ophthalmic lens having the following features: W ｆｌｏｏｒ is 0.5W or more, and the δD ｆｌｏｏｒ These are ophthalmic lenses with a diopter of 0.2D or less.

4. A lens body having a pair of opposing curved surfaces that define the lens axis, A plurality of discrete light scattering centers located in at least one area of ​​the opposing curved surfaces, each scattering center having a shape at least partially defined by its periphery, maximum depth, and maximum width, An ophthalmic lens having the following features: 、 An ophthalmic lens in which the peripheral shape is selected from the group consisting of star shape, regular polygon, dumbbell shape, pear shape, parallelogram, crescent shape, cone shape, and zigzag shape.

5. A lens body having a pair of opposing curved surfaces, A plurality of discrete light scattering centers located in at least one area of ​​the opposing curved surfaces, An ophthalmic lens having the following features: An ophthalmic lens in which the density of the plurality of light scattering centers in the area and the shape of the plurality of light scattering centers are selected such that the ophthalmic lens backscatters 12% or less of the light incident on the area of ​​the ophthalmic lens that propagates parallel to the lens axis.

6. The ophthalmic lens according to claim 1, wherein the area surrounds a clear area lacking a scattering center.

7. The ophthalmic lens according to claim 1, wherein the area is an annular area.

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

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

10. The ophthalmic lens according to claim 9, wherein the single surface is a concave surface.

11. The ophthalmic lens according to claim 9, wherein the single surface is a convex surface.

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

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

14. The ophthalmic lens according to claim 1, wherein the ophthalmic lens is an eyeglass lens or a contact lens.

15. The ophthalmic lens according to claim 1, wherein the ophthalmic lens is a plano lens, a monofocal lens, or a multifocal lens.

16. The steps include exposing the surface of an ophthalmic lens to one or more pulses of laser radiation sufficient to generate light scattering centers on the surface, The steps include: moving the laser radiation across the surface while exposing the surface, and tracing a path on the surface; A method including, The method wherein the path has a helical shape, and the light scattering center has a maximum width W in the range of 100 micrometers to 1,000 micrometers.

17. The steps include exposing the surface of an ophthalmic lens to one or more pulses of laser radiation sufficient to generate light scattering centers on the surface, The steps include: moving the laser radiation across the surface while exposing the surface, and tracing a path on the surface; A method including, The method wherein the light scattering center has a maximum width W in the range of 100 micrometers to 1,000 micrometers and a peripheral shape selected from the group consisting of star-shaped, regular polygonal, dumbbell-shaped, pear-shaped, parallelogram-shaped, crescent-shaped, conical, and zigzag.

18. A lens body having two opposing surfaces, An annular region surrounding a clear aperture, wherein the annular region has a plurality of light scattering centers that are sized and shaped to scatter incident light, An ophthalmic lens having the following features: An ophthalmic lens in which the first of the plurality of light scattering centers overlaps with the first adjacent light scattering center by a first amount, and overlaps with the second adjacent light scattering center by a second amount different from the first amount.

19. The ophthalmic lens according to claim 18, wherein the light scattering centers are arranged in a pattern including rows, and the first light scattering center and the first adjacent light scattering center are arranged in rows.

20. The ophthalmic lens according to claim 19, wherein the light scattering centers are arranged in a pattern including rows.

21. The ophthalmic lens according to claim 20, wherein the second light scattering center overlaps with the third light scattering center in the row.

22. The ophthalmic lens according to claim 20, wherein the first light scattering center overlaps with a different light scattering center, and the first light scattering center and the different light scattering centers are arranged in a row.

23. The ophthalmic lens according to claim 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.

24. The ophthalmic lens according to claim 18, wherein the light scattering centers are arranged in a pattern including circumferential and radial directions with respect to the clear aperture.

25. The ophthalmic lens according to claim 18, wherein the light scattering centers are arranged in a pattern that includes irregular variations in the spacing between pairs of adjacent light scattering centers.

26. The ophthalmic lens according to claim 18, wherein the ophthalmic lens includes a second annular region, and the light scattering centers disposed in the second annular region do not overlap.

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

28. A lens body having two opposing surfaces, An annular region surrounding a clear aperture, the annular region having a plurality of spaced-apart light scattering centers that are sized and shaped to scatter incident light, the plurality of light scattering centers arranged in a pattern including the circumferential and radial directions relative to the clear aperture, the annular region, An ophthalmic lens having the following features: An ophthalmic lens in which 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 according to claim 28, wherein the first size is uniform and the second size is variable.

30. The ophthalmic lens according to claim 28, wherein the ophthalmic lens includes a second annular region disposed between the clear aperture and the annular region, and the plurality of light scattering centers disposed in the second annular region are uniform in size in both the radial and circumferential directions.

31. The ophthalmic lens according to claim 28, wherein a portion of the plurality of light scattering centers are arranged in different patterns including irregular variations in the spacing between adjacent light scattering centers.

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

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

34. The ophthalmic lens according to claim 28, wherein the ophthalmic lens is an eyeglass lens or a contact lens.

35. A lens body having two opposing surfaces, An annular region surrounding a clear aperture, the annular region having a plurality of spaced-apart light scattering centers that are sized and shaped to scatter incident light, the plurality of light scattering centers arranged in a pattern including the circumferential and radial directions relative to the clear aperture, the annular region, An ophthalmic lens having the following features: An ophthalmic lens in which 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 according to claim 35, wherein the ophthalmic lens includes a second annular region disposed between the clear aperture and the annular region, and the plurality of light scattering centers disposed in the second annular region are uniform in size in both the radial and circumferential directions.

37. The ophthalmic lens according to claim 35, wherein a portion of the plurality of light scattering centers are arranged in different patterns including irregular variations in the spacing between adjacent light scattering centers.

38. A lens body having two opposing surfaces, An annular region surrounding a clear aperture, the annular region having a plurality of light scattering centers on at least one of the two opposing surfaces, the annular region having a depression in one of the two opposing surfaces, each light scattering center being an annular region, An ophthalmic lens having the following features: An ophthalmic lens wherein at least a portion of the plurality of light scattering centers has a depth profile with respect to one of the two opposing surfaces, the depth profile including a first trench positioned toward a first sidewall of the recess and a second trench positioned toward a second sidewall of the recess.

39. The ophthalmic lens according to claim 38, wherein the depth profile of the recess is symmetrical with respect to at least one plane.

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

41. The ophthalmic lens according to claim 38, wherein the maximum depth of the first trench is substantially equal to the maximum depth of the second trench.

42. The ophthalmic lens according to claim 41, wherein the area between the first trench and the second trench of the plurality of light scattering centers has a depth different from the maximum depth of the first trench and the maximum depth of the second trench.

43. The ophthalmic lens according to claim 38, wherein the orientation of the trench in one of the different light scattering centers varies at different locations in the annular region.

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

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

46. The ophthalmic lens according to claim 38, wherein the radial dimension of the first trench is 0.3W or less, and W is the maximum width of one of the plurality of light scattering centers.

47. The ophthalmic lens according to claim 38, wherein the depth profile includes one or more additional trenches between the first trench and the second trench.

48. The process involves exposing a first location of the lens material of an ophthalmic lens to focused laser radiation from a laser beam, thereby forming a first sidewall portion with optically scattering characteristics on the surface of the ophthalmic lens. The steps include: exposing the ophthalmic lens to the focused laser radiation while causing a relative motion between the laser beam and the ophthalmic lens in a first direction so as to move away from the first side wall portion; The steps include exposing a second location of the ophthalmic lens to the focused laser radiation to form the second sidewall portion having the optically scattering characteristics, A method including, A method comprising the step of exposing the first and second locations of the ophthalmic lens to create a depression in the lens material, the depression having a depth profile with respect to the surface of the ophthalmic lens, the depth profile including a first trench positioned toward the first sidewall and a second trench positioned toward the second sidewall of the depression.

49. The method according to claim 48, wherein the step of exposing the first location includes exposing the first location of the ophthalmic lens over a first time period, and the step of exposing the second location includes exposing the second location over a second time period that is longer than the first time period.

50. The method according to claim 48, wherein the first side wall portion and the second side wall portion form a circular optically scattering feature.

51. The method according to claim 48, wherein the depth of the first trench is substantially equal to the depth of the second trench.

52. The method according to claim 48, wherein the step of causing relative motion generates an area between the first trench and the second trench of the depression having a depth different from the depth of the first trench and the depth of the second trench.

53. A lens body having two opposing surfaces, An annular region surrounding a clear aperture, wherein the annular region has a plurality of light scattering centers that are sized and shaped to scatter incident light, An ophthalmic lens having the following features: An ophthalmic lens wherein at least some of the diameters of the plurality of light scattering centers are in the range of approximately 1.001 mm to approximately 1.5 mm, and the spacing between the plurality of light scattering centers varies over the annular region.

54. The light scattering centers are arranged in a pattern that includes the circumferential and radial directions with respect to the clear aperture. The ophthalmic lens according to claim 53, wherein the 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 a variable size.

55. The ophthalmic lens according to claim 54, wherein the ophthalmic lens includes a second annular region disposed between the clear aperture and the annular region, and the light scattering centers disposed in the second annular region are uniform in size in both the radial and circumferential directions.

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

57. The ophthalmic lens according to claim 56, wherein the light scattering centers are arranged in a pattern including rows, and the first light scattering center and the adjacent light scattering centers are arranged in rows.

58. The ophthalmic lens according to claim 57, wherein the plurality of light scattering centers are arranged in a pattern including rows.

59. The ophthalmic lens according to claim 53, wherein the plurality of light scattering centers are arranged in a pattern that includes irregular variations in the spacing between adjacent scattering centers.

60. Each light scattering center includes a depression in one of the two opposing surfaces of the ophthalmic lens. The ophthalmic lens according to claim 53, wherein at least a portion of the plurality of light scattering centers has a depth profile with respect to one of the two opposing surfaces of the ophthalmic lens, the depth profile includes a first trench positioned toward a first sidewall of the light scattering center and a second trench positioned toward a second sidewall of the light scattering center.

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

62. The ophthalmic lens according to claim 60, wherein the depth of the first trench is substantially equal to the depth of the second trench.

Images