Ophthalmic lens and eyeglasses including same

Abstract

The utility model relates to an ophthalmic lens and glasses comprising the same. An ophthalmic lens includes: a lens body having two opposing curved surfaces; and a region having a plurality of light scattering centers in the lens body and / or on at least one of the two opposing curved surfaces, characterized in that the light scattering centers are sized and shaped so as to scatter incident light, the region corresponding to a peripheral field of view of a user of the ophthalmic lens, the diameter of at least some of the plurality of light scattering centers is in the range of 1.001 mm to 1.5 mm, and the spacing between the light scattering centers varies through the annular region.

Description

[0001] This application is a divisional application of a patent application with application number 202322290260.4 filed on August 24, 2023, and utility model name “Ophthalmic lens with large light scatterer for treating myopia”. Technical Field

[0002] The utility model is characterized by an ophthalmic lens for treating myopia and reducing the progression of myopia and a manufacturing method thereof. Background Art

[0003] The eye is an optical sensor in which light from an external source is focused through the lens onto the surface of the retina, which is a series of wavelength-dependent photoelectric sensors. Each of the various shapes that the eye lens can adopt is associated with a focal length at which external light rays are optimally or nearly optimally focused to produce an inverted image on the retinal surface that corresponds to the external image observed by the eye. In each of the various shapes that the eye lens can adopt, the eye lens optimally or nearly optimally focuses light emitted by or reflected from external objects within a certain range of distances from the eye, and less optimally focuses or fails to focus objects located outside this distance range.

[0004] In people with normal vision, the axial length of the eye, or the distance from the lens to the retinal surface, corresponds to the focal length at which distant objects are nearly in optimal focus. The eye of a person with normal vision focuses on distant objects without tense input to the muscles that exert force to change the shape of the eye's lens, a process known as "accommodation." As a result of accommodation, normal people focus on closer nearby objects.

[0005] However, many people suffer from eye length-related disorders, such as myopia ("nearsightedness"). 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, a myopic person can see nearby objects clearly, but distant objects are blurry. Although myopic people are generally able to accommodate, the average distance at which they can focus on objects is shorter than that of a person with normal vision.

[0006] Typically, infants are born farsighted, with an eye length that is shorter than required for optimal or near-optimal focus on distant objects without accommodation. During the normal development of the eye, known as "emmetropization," the axial length of the eye increases relative to the other dimensions of the eye to a length that provides near-optimal focus of distant objects without accommodation. Ideally, biological processes would maintain the relative length of the eye to the size of the eye at a near-optimal level 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 beyond the length that provides near-optimal focus of distant objects, resulting in increasingly pronounced myopia.

[0007] Myopia is believed to be influenced by both behavioral and genetic factors. Therefore, myopia can be alleviated by a therapeutic device that addresses the behavioral factors. For example, a therapeutic device for treating eye length-related diseases (including myopia) is described in U.S. Publication No. 2011 / 0313058A1. Utility Model Content

[0008] An ophthalmic lens is disclosed, comprising: a lens body having two opposing surfaces; and an annular zone surrounding a clear aperture, wherein the annular zone has a plurality of light scattering centers in the lens body and / or on at least one of the two opposing surfaces, the light scattering centers being sized and shaped to scatter incident light, wherein at least some of the plurality of light scattering centers have diameters in the range of about 1.001 mm to about 1.5 mm, and the spacing between the light scattering centers varies across the annular zone.

[0009] The disclosed eyeglasses reduce the signals in the retina that are responsible for eye length growth. For example, the eyeglass lenses are made using, for example, polycarbonate or Trivex lens blanks that have been treated by forming a pattern of scattering centers or "dots," optionally with a dot-free aperture on the viewing axis. The dots scatter incident light that would otherwise be focused by the lens, resulting in reduced contrast in the retinal image. The reduced contrast reduces eye growth associated with myopia progression, particularly in children. The optional dot-free aperture, typically located on the visual axis corresponding to the wearer's distance vision and allowing the user to experience maximum visual acuity when viewing objects on the axis, while objects at the periphery of the user's field of view are viewed with reduced contrast and acuity.

[0010] Control of the size and shape of the dots is used to tailor the light scattering properties of the lens. One function is to increase forward scattering into directions where the scattered light helps reduce image contrast in the wearer's peripheral vision. Another function is to reduce backscattered light. Reducing backscattered light can reduce the conspicuity of the dot pattern. Increased scattering in the forward direction can reduce the total number of dots needed to provide a therapeutic effect.

[0011] A laser exposure method for forming a spot having a desired shape is also disclosed. The exposure method can include using a laser scanning path that can be implemented efficiently to increase the overall throughput of the laser system by reducing the exposure time or cycle time.

[0012] Among other advantages, the disclosed embodiment features glasses include features that reduce the signals in the retina responsible for eye length growth on the lenses of both eyes without reducing the user's on-axis vision in either eye to a level that is disruptive to the user. For example, providing a dot pattern that moderately obscures the wearer's peripheral vision or reduces contrast while allowing normal on-axis viewing through the clear aperture allows for all-day, everyday use by the wearer. The disclosed embodiments can also provide therapeutic benefits to a user for both eyes using only one pair of glasses, as opposed to methods that involve alternating between different glasses.

[0013] Additionally, the dot pattern may be substantially unnoticeable to others, particularly if the dot pattern is clear and colorless and / or when using contact lenses. The subtlety of the dot pattern may enable more consistent use by certain wearers, particularly children, who may otherwise be self-conscious about using a more conspicuous device in daily life (e.g., at school or among other peers). For example, a gradient dot pattern may be used to reduce the conspicuity of the dot pattern to third parties.

[0014] The disclosed embodiments can allow dot patterns for mitigating eye lengthening to be efficiently and economically formed on conventional ophthalmic lenses, such as by forming the dot pattern on a surface or body of the lens. BRIEF DESCRIPTION OF THE DRAWINGS

[0015] Figure 1A An example of a pair of glasses incorporating ophthalmic lenses for reducing the progression of myopia is shown.

[0016] Figure 1B It shows that Figure 1A An ophthalmic lens is shown prior to edge sealing.

[0017] Figure 1C Shown in Figure 1B A plan view of the dot pattern in the contrast-reduced region of the lens is shown.

[0018] Figure 2 It is shown from Figure 1BSchematic diagram of light scattering by an ophthalmic lens is shown.

[0019] Figure 3A A cross-sectional view of an example point consisting of a depression in the lens surface is shown.

[0020] Figure 3B A cross-sectional view of an example point consisting of protrusions on the lens surface is shown.

[0021] Figure 3C A cross-sectional view of another example point consisting of a depression in the lens surface is shown.

[0022] Figure 3D A cross-sectional view of a further example point consisting of a depression in the lens surface is shown.

[0023] Figure 4A-4S A plan view of the path around an example point is shown.

[0024] Figure 5A is a graph comparing the amount of light rays hitting the retina for five different simulated dot shapes.

[0025] Figure 5B is a graph comparing the amount of backscattered light for five different simulated point shapes.

[0026] Figure 6 is a schematic diagram of an example laser system for forming a spot on a lens surface.

[0027] Figure 7 is a plan view of an example laser exposure path for forming dots.

[0028] Figure 8 is a plan view of another example laser exposure path for forming dots.

[0029] Fig.9A and Fig. 9B is used Figure 8 Top view of the image of the two points formed by the paths shown.

[0030] Fig. 9C yes Fig. 9B A cross-sectional profile at one of the points shown.

[0031] Fig. 10A and Fig. 10B is used Figure 7 Top view of the image of the two points formed by the paths shown.

[0032] Fig. 10C yes Fig. 10B A cross-sectional profile at one of the points shown.

[0033] Fig.11Ais a plan view of an example laser exposure path for forming spots along the path using discrete pulses of laser radiation.

[0034] Fig. 11B and Fig. 11C is used Fig.11A Top view of the image of the two points formed by the paths shown.

[0035] Fig.11D yes Fig. 11C A cross-sectional profile at one of the points shown.

[0036] Fig. 12A is an example of a dot pattern on an ophthalmic lens where the dots are burned in by a laser.

[0037] Fig. 12B yes Fig. 12A A partial enlarged view of the dot pattern.

[0038] Fig. 12C is Fig. 12B Magnified cross-sectional view of the point obtained at CC.

[0039] Fig.13 is a flow chart of a method of forming spots using a laser system with laser burning for forming trenches.

[0040] Fig.14 Example dot patterns with dots of different sizes are shown.

[0041] Fig.15 Another example dot pattern with dots of different sizes is shown.

[0042] Fig.16 Further example dot patterns with dots of different sizes are shown.

[0043] Fig.17 An example dot pattern with overlapping dots is shown.

[0044] Fig.18 An example dot pattern with rows of overlapping dots is shown.

[0045] Fig.19 Another example dot pattern is shown having overlapping and non-overlapping rows and columns of dots.

[0046] Fig. 20 Another example dot pattern is shown having a radial array of overlapping dots of different sizes.

[0047] Fig.21 Another example dot pattern is shown having a radial array and overlapping and non-overlapping dots of varying sizes.

[0048] Fig. 22Another example dot pattern is shown with overlapping and non-overlapping dots of different sizes.

[0049] In the drawings, like reference numerals denote like elements. DETAILED DESCRIPTION

[0050] See also Figure 1A-Figure 1C , shows a pair of glasses 100 for reducing myopia progression. The glasses 100 treat both eyes simultaneously without significantly affecting clear vision on axis for the wearer. Furthermore, the glasses are strong and unobtrusive enough that the wearer can carry out the same daily activities without the glasses failing or being embarrassed about their appearance, which is particularly desirable since glasses are often used to stop children's eyes from growing longer.

[0051] The glasses 100 are composed of a pair of frames 101 and ophthalmic lenses 110a and 110b installed in the frames 101. Generally, the ophthalmic lenses can be planar lenses, single-vision lenses (e.g., lenses with positive or negative optical power), or multi-vision lenses (e.g., bifocals or progressive lenses). The ophthalmic lenses 110a and 110b have clear apertures 120a and 120b, respectively, which are surrounded by contrast-reduced regions 130a and 130b, respectively. The positions of the clear apertures 120a and 120b can coincide with the wearer's distance vision, while the contrast-reduced regions 130a and 130b correspond to the wearer's peripheral field of vision, and the wearer's gaze direction corresponds to distance vision. Figure 1B In FIG. 1 , lens 110a is shown pre-edge sealed.

[0052] In general, the size and shape of the clear apertures 120a and 120b can vary. Typically, the clear apertures provide a viewing cone for the wearer for which their vision is optimally corrected (e.g., to 20 / 15 or 20 / 20). In some examples, the maximum size of the apertures ranges 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). Where the aperture is circular, for example, as Figure 1A and Figure 1B As shown, this dimension corresponds to the diameter D of the circle 120 , but non-circular (eg, elliptical, polygonal, tear-shaped) apertures may also be used.

[0053] The clear aperture can form a solid angle of about 30 degrees or less (e.g., about 25 degrees or less, about 20 degrees or less, about 15 degrees or less, about 12 degrees or less, about 10 degrees or less, about 9 degrees or less, about 8 degrees or less, about 7 degrees or less, about 6 degrees or less, about 5 degrees or less, about 4 degrees or less, about 3 degrees or less) in the viewer's field of view. The solid angles formed in the horizontal and vertical viewing planes can be the same or different.

[0054] In some cases, lenses 110a and 110b can include no clear aperture and the region of reduced contrast occupies the entire on-axis field of view.

[0055] See also Figure 1B , the area of ​​reduced contrast 130a extends to a radius less than the radius of the pre-sealed lens, occupying an annular area around the clear aperture 120a. Typically, the area of ​​reduced contrast of the pre-sealed lens extends far enough so that after the lens is edge-sealed and mounted in the frame 101, the desired level of light scattering is achieved for the user's peripheral vision regardless of the user's viewing direction when wearing the glasses. The area of ​​reduced contrast 130a can have a maximum dimension (e.g., a diameter D in the case of a circular area) in the range of about 3 cm to about 9 cm (e.g., about 4 cm or more, about 5 cm or more, about 6 cm or more, about 7 cm or more, such as about 8 cm or less). 130 ). Although the region of reduced contrast 130a has a circular perimeter, other shapes are possible (eg, elliptical, polygonal, etc.).

[0056] See Figure 1C , the regions of reduced contrast 130a and 130b include scattering centers, also referred to as "spots" 112, which reduce the contrast of objects in the wearer's peripheral vision by scattering light passing through these regions toward the wearer's eyes. The lens region between the spots 140 corresponds to the original (e.g., Rx) lens surface that provides a sharp, focused image to the wearer. The result of the regions of reduced contrast 130 is to provide the wearer with a resolvable image, corrected for any refractive errors of the wearer, whose contrast level is reduced compared to the on-axis image viewed through the clear apertures 120a and 120b.

[0057] In general, the region of reduced contrast of a lens includes hundreds, or thousands, of dots, and the size of the dots can be the same on each lens or can vary. For example, the size can increase or decrease as a function of the location of the dot, e.g., measured from the clear aperture and / or as a function of the distance from the edge of the lens. In some examples, the size of the dot varies monotonically (e.g., monotonically increases or monotonically decreases) with increasing distance from the center of the lens. In some cases, the monotonic increase / decrease in size includes linearly changing the diameter of the protrusion as a function of the distance from the center of the lens.

[0058] exist Figure 1C The dots are shown irregularly arranged on the lens surface. Generally speaking, the dots are arranged so that they collectively provide enough contrast reduction to the viewer's periphery to reduce myopia. Generally, a smaller dot spacing will result in a greater contrast reduction. Generally, the dots can be spaced apart or overlap each other. For spaced-apart dots, the distance between adjacent dots can be from 0.05 mm (e.g., about 0.1 mm or more, about 0.15 mm or more, about 0.2 mm or more, about 0.25 mm or more, about 0.3 mm or more, about 0.35 mm or more, about 0.4 mm or more, about 0.45 mm or more, about 0.5 mm or more, about 0.55 mm or more, about 0.6 mm or more, about 0.65 mm or more, about 0.7 mm or more, about 0.75 mm or more) to about 2 mm (e.g., about 1.9 mm or less, about 1.8 mm or less, about 1.7 mm or less, about 1.6 mm or less, about 1.5 mm or less, about 1.4 mm or less, about 1.3 mm or less, about 1.2 mm or less, about 1.1 mm or less, about 1 mm or less, about 0.9 mm or less, about 0.8 mm or less).

[0059] In general, the coverage of the lens by the points can be varied as desired. Here, coverage refers to the proportion of the total area of ​​the lens projected onto the xy plane corresponding to the point. Generally, lower point coverage will produce lower scattering than higher point coverage (assuming that the individual points are discrete, i.e., they do not merge to form larger points). Point coverage can vary from 10% or greater to about 75%. For example, point coverage can be 15% or greater, 20% or greater, 25% or greater, 30% or greater, 35% or greater, 40% or greater, 45% or greater, such as 50% or 55%. Point coverage can be selected based on the user's comfort, for example, to provide a sufficiently comfortable level of peripheral vision that the wearer will voluntarily wear the glasses for long periods of time (e.g., all day).

[0060] It is believed that light from the scene incident on the lens of the reduced contrast regions 130a and 130b between the dots contributes to obtaining an image of the scene on the user's retina, while light from the scene incident on the dots does not. In addition, light incident on the dots is still transmitted to the retina, thereby having the effect of reducing image contrast without significantly reducing the light intensity at the retina. Therefore, it is believed that the amount of contrast reduction in the user's peripheral field of view is related to (e.g., approximately proportional to) the proportion of the surface area of ​​the reduced contrast region covered by the dots. Typically, the dots occupy at least 10% (e.g., 20% or more, 30% or more, 40% or more, 50% or more, such as 90% or less, 80% or less, 70% or less, 60% or less) of the area of ​​the reduced contrast regions 130a and 130b (as measured in the xy plane).

[0061] In general, the dot pattern reduces the contrast of the image of objects in the wearer's peripheral vision without significantly reducing the viewer's vision in this area. Peripheral vision here refers to the field of view outside the field of view of the clear aperture. The image contrast in these zones can be reduced by 40% or more (e.g., 45% or more, 50% or more, 60% or more, 70% or more, 80% or more) relative to the image contrast observed using the clear aperture of the determined lens. The contrast reduction can be set as needed for each case. It is believed that a typical contrast reduction will be in the range of approximately 50% to 55%. For very mild cases, a contrast reduction of less than 50% can be used, while a contrast reduction of more susceptible subjects may require a contrast reduction of more than 55%. Based on subjective refraction determinations, peripheral vision can be corrected to 20 / 30 or better (e.g., 20 / 25 or better, 20 / 20 or better) while still achieving meaningful contrast reduction.

[0062] Here, contrast refers to the difference in brightness between two objects in the same field of view. Therefore, contrast reduction refers to the change in this difference.

[0063] Contrast and contrast reduction can be measured in a variety of ways. In some embodiments, contrast can be measured based on the brightness differences between different parts of a standard pattern, such as a checkerboard of black and white squares, obtained under controlled conditions through the clear aperture of a lens and a dot pattern.

[0064] Alternatively, or in addition, contrast reduction can be determined based on the optical transfer function (OTF) of the lens (see, e.g., http: / / www.montana.edu / jshaw / documents / 18%20EELE582_S15_OTFMTF.pdf). For OTF, contrast is specified for the transmission of a stimulus in which light and dark areas are sinusoidally modulated at different "spatial frequencies." These stimuli look like alternating light and dark bars, with the spacing between the bars varying over a certain range. For all optical systems, contrast transmission is lowest for the sinusoidally varying stimulus with the highest spatial frequency. The relationship that describes contrast transmission for all spatial frequencies is the OTF. The OTF can be obtained by the Fourier transform of the point spread function. The point spread function can be obtained by imaging a point light source through a lens onto a detector array and determining the distribution of light from the point on the detector.

[0065] In case of conflicting measurements, OTF technology is preferred.

[0066] In some embodiments, contrast can be estimated based on the ratio between the area of ​​the lens covered by the dots and the area of ​​the clear aperture. In this approximation, it is assumed that all light hitting the dots is evenly dispersed across the retinal area, which reduces the amount of available light in brighter areas of the image, thereby increasing light for darker areas. Thus, the contrast reduction can be calculated based on light transmittance measurements made through the clear aperture of the lens and the dot pattern.

[0067] Contrast can also be measured clinically by measuring the change in performance of an observer wearing the lens on a visual acuity (such as a Snellen or ETDRS letter chart) and / or a contrast sensitivity test (e.g., a Pelli Robson chart). The contrast change can be less than 1 line (i.e., 5 letters) of vision, about 0.5 lines, 1 line, 2 lines, or 3 lines or more. This can also be measured in units of LogMAR of less than 0.05 or about 0.05, 0.10, 0.20, or 0.30 or more.

[0068] As previously described, in general, the size, spacing, and arrangement of the dot pattern can vary. In some embodiments, the dot pattern is characterized by a gradient, such as the size and / or spacing of the dots. The dot pattern can be characterized by a gradient in the efficiency of the dots (e.g., due to a gradient in the refractive index mismatch and / or the shape of each dot). A gradient dot pattern can reduce the conspicuity of the pattern. For example, a gradual transition from a transparent portion of a lens to a scattering portion may be less noticeable than a sharp transition.

[0069] Lenses 110a and 110b can be formed from off-the-shelf lenses. Lenses can be made from conventional ophthalmic lens materials, such as polycarbonate or The lens can include one or more coatings or other surface treatments including, for example, hard coatings, photochromic coatings, blue filters, anti-reflection coatings, and the like.

[0070] In general, ophthalmic lenses 110a and 110b can be transparent or tinted. That is, the lenses can be optically transparent to all visible wavelengths, appearing clear and / or colorless, or can include spectral filters, appearing tinted. For example, an ophthalmic lens may include a filter that reduces the amount of red light transmitted to the wearer. It is believed that overstimulation of the L cones in the human eye (especially in children) can lead to non-optimal eye elongation and myopia. Therefore, spectrally filtering red light using an ophthalmic lens can further reduce myopia in the wearer.

[0071] In general, the dots 112 can be formed as protrusions and / or grooves on one or both surfaces of each lens, and / or as scattering inclusions in the lens material itself. In some examples, the dots can be formed by an array of protrusions on each surface (e.g., back or front surface) of lenses 110a and 110b.

[0072] The protrusions can be formed from an optically transparent material having a similar refractive index to the underlying lens, which is 1.60 for polycarbonate. For example, in embodiments where the lens is formed from polycarbonate, the protrusions can be formed from a polymer having a similar refractive index to PC, such as from a light activated polyurethane or epoxy-based plastic. In addition to PC, the lens itself can be made from allyl diglycol carbonate plastic, polyurethane-based monomers, or other impact-resistant monomers. Alternatively, the lens can be made from a higher density, high-index plastic with a refractive index greater than 1.60. In some embodiments, the lens is made from an optically transparent material with a lower refractive index (e.g., 1.50 for CR39 and 1.53 for Trivex).

[0073] Each dot 112 is sized and shaped to scatter light incident on that dot. Typically, the dot scatters a portion of the incident light forward and a portion of the incident light backward. The forward scattered light typically leaves the lens through the side opposite to where it was incident, while the backward scattered light is scattered from the lens on that side. The light scattering is as follows: Figure 2 , which shows a lens 110a with a scattering center 112 on the front surface of the lens. The lens axis 203 is shown for reference, for example corresponding to the rotational symmetry axis of the lens, where the lens only corrects for spherical aberration.

[0074] Four incident light rays 206, 208, 210, and 212 are shown, each incident on a different point 112. Depending on the angle of incidence of the rays and the shape of the point, the light can be forward scattered (rays 214 and 218) and / or back scattered (rays 216 and 220). Depending on the forward scattering angle at the time and the wearer's visual axis, the forward scattered light entering the eye 224 can be incident on the wearer's fovea or away from the wearer's fovea, or can be completely away from the retina. Generally, scattered light (unlike other light focused by the lens) is not imaged on the wearer's retina. Scattered light is incident on the wearer's fovea and reduces the contrast of the wearer's foveal vision, which may be undesirable. As previously described, scattered light incident on the retina away from the fovea can reduce the contrast of the wearer's peripheral vision, thereby reducing myopia progression. This forward scattered light can be considered "therapeutic light". In some (but not all) cases, other forward scattered light, such as scattered light incident outside the fovea or the retina's peripheral vision, is not considered therapeutic. Therefore, it may be desirable to scatter light forward into a direction that will contribute to peripheral visual contrast reduction, rather than foveal contrast reduction. Alternatively, forward scattered light that contributes to foveal contrast reduction may be acceptable in some cases.

[0075] Generally, light scattered into the cone that contributes to image contrast reduction in the peripheral field of view is considered narrow-angle forward scattered light, while light outside the cone is considered wide-angle forward scattered light. Figure 2 223 can be used to distinguish between narrow angle scattering and wide angle scattering. Light scattered inside the cone, such as light 218, is narrow angle forward scattered light, while light scattered outside the cone, such as light 214, is wide angle scattering. The cone angle can be used for narrow angle scattering in the range of 1 degree to 5 degrees. In some examples, the cone angle for narrow angle scattering can be 2.5 degrees.

[0076] Some of the incident light is backscattered, for example, incident light rays 208 and 212 are backscattered as backscattered light rays 216 and 220. The backscattered light can be seen by people other than the wearer, which makes these points conspicuous to people viewing 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 entering the narrow angle, until a threshold amount of peripheral image contrast reduction sufficient to have the above-mentioned therapeutic effect is achieved.

[0077] For light incident on the area with reduced contrast, a scanning scatterometer can be used to measure the amount of scattered light forward scattered and / or back scattered. A scanning scatterometer is an instrument with a light source (such as a laser) and a detector (such as a single pixel detector). The sample is illuminated by a collimated beam from the light source, and the detector scans on a sphere around the sample to generate a map of where the light goes. Using this method, the total amount of light incident on the area with reduced contrast of backscattering 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, 1% or less. The percentage of backscattered scattered light can be 50% or less, 40% or less, 30% or less, 20% or less, 10% or less or less than 10%, such as 9% or less, 8% or less, 7% or less, 6% or less, 5% or less, 4% or less, 3% or less, 2% or less, such as 1%. The percentage of the scattered light scattered forward can be 50% or more, 60% or more, 70% or more, 80% or more, 90% or more, 91% or more, 92% or more, 93% or more, 94% or more, 95% or more, 96% or more, 97% or more, 98% or more, such as 99%. The percentage of the scattered light scattered forward to the narrow-angle scattering direction (as described above) can be 50% or more, 60% or more, 70% or more, 80% or more, 90% or more, such as 95%.

[0078] In some cases, the amount of forward scattered and / or backscattered light can be determined by optical computer simulation using, for example, commercially available optical design software such as Zemax (from AnSys) or Code V (from Synopsys). Using this approach, the total amount of light incident on the backscattered contrast-reduced region can be 12% or less, 10% or less, 9% or less, 8% or less, 7% or less, 6% or less, 5% or less, 4% or less, 3% or less, 2% or less, 1% or less. The percentage of backscattered scattered light can be 50% or less, 40% or less, 30% or less, 20% or less, 10% or less, or less than 10%, such as 9% or less, 8% or less, 7% or less, 6% or less, 5% or less, 4% or less, 3% or less, 2% or less, or 1% or less. The percentage of backscattered scattered light can be 50% or less, 40% or less, 30% or less, 20% or less, 10% or less, or less than 10%, such as 9% or less, 8% or less, 7% or less, 6% or less, 5% or less, 4% or less, 3% or less, 2% or less, or 1%. The percentage of the scattered light scattered forward can be 50% or more, 60% or more, 70% or more, 80% or more, 90% or more, 91% or more, 92% or more, 93% or more, 94% or more, 95% or more, 96% or more, 97% or more, 98% or more, such as 99%. The percentage of the scattered light scattered forward to the narrow-angle scattering direction (as described above) can be 50% or more, 60% or more, 70% or more, 80% or more, 90% or more, such as 95%.

[0079] Thus, in general, the dot pattern in the contrast-reduced regions 130a and 130b and the shape of each dot are selected based on various design parameters to provide the desired degree of light scattering to provide the best therapeutic effect while minimizing the amount of backscattered light. Typically, these design parameters include the dot pattern (i.e., dot density, dot density distribution, relative positions of the dots, etc.), their size and shape, their refractive index, and other properties, such as the transmission and reflection characteristics of the dots at various wavelengths. Ideally, the dot pattern is selected to provide high visual acuity on the fovea and reduce image contrast in other parts of the retina while being sufficiently low in discomfort to the wearer to allow for long, continuous wear. For example, it is best for children to wear glasses comfortably for most, if not all, of the day. The dot size, shape, and dot pattern can also be selected to provide a relatively small amount of backscattered light.

[0080] Examples of dot patterns are described in US20190033619A1, entitled “Ophthalmic lenses for treating myopia”, and US20190235279A1, entitled “Ophthalmic lenses with light scattering for treating myopia”, the entire contents of which are incorporated herein in their entirety. More examples of dot patterns are described below.

[0081] A variety of different metrics can be used to evaluate the performance of dot patterns in order to optimize them for glasses with myopia reduction. For example, dot patterns can be optimized empirically, for example, based on physical measurements of lenses with different dot patterns. For example, light scattering can be characterized according to haze measurements, such as international test standards for haze (e.g., ASTM D1003 and BSEN ISO 13468). A traditional haze meter can be used, for example, a BYK-Gardne haze meter (such as a Haze-Gard Plus instrument), which measures the amount of light fully transmitted through the lens, the amount of light not disturbed by transmission (e.g., within 0.5 degrees), the amount of light deflected more than 2.5 degrees, and clarity (amount within 2.5 degrees). Other instruments can also be used to characterize light scattering in order to empirically optimize scattering patterns. For example, an instrument (e.g., an instrument from Hornell) that measures light diffusion by measuring light about 2.5 degrees in an annular ring can be used.

[0082] Alternatively, or additionally, the dot pattern can be optimized by computer modeling software (eg, Zemax or Code V).

[0083] Alternatively, or additionally, the dot pattern can be optimized empirically by designing various patterns and measuring forward and backscatter using the methods described above.

[0084] In some examples, the dot shape and dot pattern can be designed based on the optimization of a point spread function that represents an image of the scattering centers on the retina. For example, the size, shape, and spacing of the scattering centers can be varied to evenly distribute the illumination of the retina so that the retina outside the fovea is evenly covered with scattered light to reduce (e.g., minimize) the contrast of that area of ​​the retina.

[0085] Alternatively, or in addition, the dot shape and dot pattern can be designed based on optimization of the modulation transfer function, which refers to the spatial frequency response of the human visual system. For example, the size, shape, and spacing of the scattering centers can be changed to smooth the attenuation of a range of spatial frequencies. The design parameters of the dot pattern can be changed as needed to increase or decrease certain spatial frequencies. Typically, the spatial frequencies of visual interest are 18 cycles per degree on the fine side and 1.5 cycles per degree on the coarse side. The dot pattern can be designed to provide an increased signal at certain subsets of spatial frequencies within this range.

[0086] As described above, the point can be provided on one or both surfaces of the lens, or within the lens itself. For a point formed on a lens surface, the point can be formed as a protrusion on the lens surface or as a depression in the surface. Examples of depressions and protrusions are as follows: Figure 3A and Figure 3B As shown. Figure 3A , point 301 is formed as a depression in lens surface 310. In the cross-sectional profile, the shape of point 301 is characterized by a width or lateral dimension W and a depth D. The width refers to the lateral dimension from one edge of the point (i.e., where the point meets the lens surface) to the opposite edge. The depth refers to the vertical dimension of the point measured from the edge of the point to the base of the point. Here, the depression has a parabolic profile, symmetrical about a central vertical axis, which axis corresponds to the surface normal of the lens surface 310 at the center of the point. The profile of the point can be the same in other cross sections (e.g., for a point with a circular perimeter shape), or can vary for different cross sections. Examples of point perimeter shapes are discussed below.

[0087] In general, the width and depth, as well as the shape, can vary as desired. As described below, the width and depth affect how the dots scatter light. In some examples, the width of the dots (e.g., the maximum width at which the width varies with cross-section) ranges from 10 μm to 2,000 μm (e.g., 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, 1000 μm or more, 1100 μm or more, 1200 μm or more, 1300 μm or more, 1400 μm or more, 1500 μm or more, 1600 μm or more, 1700 μm or more, 1800 μm or more, 1900 μm or more, 2000 μm or more, 2100 μm or more, 2200 μm or more, 2300 μm or more, 2400 μm or more, 2500 μm or more, 2600 μm or more, 2700 μm or more, 2800 μm or more, 2900 μm or more, 3100 μm or more, 3200 μm or more, 3300 μm or more, 3400 μm or more, 3500 μm or more, 3600 μm or more, 3700 μm or more, 3800 μm or more, 3900 μm or more, 4000 μm or more, 700μm or more, 800μm or more, 900μm or more, and such as 1750μm or less, 1500μm or less, 1250μm or less, 1000μm or less, 900μm or less, 800μm or less, 700μm or less, 600μm or less, 500μm or less, such as in the range of 100μm to 400μm, 200μm to 350μm). The depth of the point 301 ranges from 2 μm to 500 μm (e.g., 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, 20 0μm or greater, and 450μm or less, 400μm or less, 350μm or less, 300μm or less, 250μm or less, 200μm or less, 150μm or less, 120μm or less, 100μm or less, 50μm or less, 30μm or less, 20μm or less, such as in the range of 10μm to 150μm, such as in the range of 20μm to 100μm, such as in the range of 30μm to 80μm).

[0088] The depth of the recess can be less than the width. For example, the D / W ratio 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 such as 8 / 10 or less, 7 / 10 or less, 6 / 10 or less, 1 / 2 or less, 1 / 3 or less, 1 / 4 or less).

[0089] In some examples, the depth is 20 μm or less, and the width (eg, maximum width) is 100 μm or more.

[0090] It is believed that points having a depth less than their width, such as the D / W described above, can have reduced backscattering compared to points having a depth similar to or greater than their width. Reduced backscattering can also generally be associated with shallower points (e.g., points having a depth of 50 μm or less). Without wishing to be bound by theory, the reduced backscattering may be due to fewer light ray paths that cause multiple reflections, which can increase where the depth or aspect ratio of the point increases.

[0091] Figure 3B A point formed as a protrusion 302 is shown, which has a width W and a height (e.g., maximum height) H. The width range of the protrusion 302 can be the same as that of the depression 301. The height range can be the same as the range of the depth D of the depression 301.

[0092] Although the profiles of points 132 and 134 are parabolic respectively on the cross-sections depicted in Figure 3A and Figure 3B points can have other profile shapes. For example, in some cases, the point is crater-shaped, having a central depression that extends to a depth below the lens surface surrounded by an edge 316 that extends to a height above the lens surface. An example of a crater-shaped point 303 is shown in Figure 3C The width of the point 303 is W and the depth is D, as defined above. In addition, the width of the depression 313 is WD (<W). The edge 316 has a height (e.g., the maximum height where the height varies around the perimeter) HR and a width (e.g., the maximum width where the width varies around the perimeter) WR. W and D can be within the above ranges. WD can be 1,500 μm or less (e.g., 1,000 μm or less, 800 μm or less, 700 μm or less, 600 μm or less, 500 μm or less, 400 μm or less, 300 μm or less, 250 μm or less, 200 μm or less, 150 μm or less, and such as 50 μm or greater, 75 μm or greater, 100 μm or greater, 120 μm or greater, 150 μm or greater, 200 μm or greater).

[0093] HR can be less 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).

[0094] WR can be 20 μm or less (eg, 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).

[0095] The dots can have irregular surfaces. Examples of dots in the form of pits 304 with irregular surfaces are Figure 3D 31. Here, the depth D and width W of the pit 304 are defined as before. The rim 317 has a height HR and width as described above. In addition, the central depression 314 is characterized by sidewalls 318 and a bottom 319. The bottom 319 extends with a width WF and is characterized by an irregular surface with a height variation dF. Here, WF is measured from the base of the sidewall 318a to the base of the opposite sidewall 318b. The base of the sidewall can be identified as the location of the local minimum in the depression cross-sectional surface profile, where the height of the bottom begins to increase.

[0096] When the sidewalls are vertical, WD=WF. Typically, WD will be the same as or greater than WF. For example, WF can be 0.95 WD or less (e.g., 0.9 WD or less, 0.8 WD or less, 0.75 WD or less, 0.7 WD or less, 0.65 WD or less, 0.6 WD or less, 0.55 WD or less, 0.5 WD or less, 0.45 WD or less, 0.4 WD or less). In some examples, WF is 500 μm or less (e.g., 400 μm or less, 300 μm or less, 250 μm or less, 200 μm or less, 150 μm or less, 100 μm or less, 80 μm or less, such as approximately 20 μm or more, 50 μm or more, 75 μm or more, 100 μm or more).

[0097] In some cases, a small value of dF corresponds to a smooth and flat bottom 319. In an example, dF can be 0.5D or less (e.g., 0.4D or less, 0.3D or less, 0.2D or less, 0.15D or less, 0.1D or less, 0.075D or less, 0.05D or less). dF can be 50 μm or less (e.g., 40 μm or less, 30 μm or less, 20 μm or less, 10 μm or less, 5 μm or less, 3 μm or less, 2 μm or less, such as 1 μm or more, 2 μm or more, 3 μm or more, 5 μm or more, 8 μm or more, 10 μm or more).

[0098] In some examples, WF is 0.5W or greater and dF is 0.2D or less.

[0099] Without wishing to be bound by theory, it is believed that a dot having relatively steep sidewalls (e.g., where WD is not much greater than WF), being relatively shallow (e.g., D is 50 mm or less), and having a relatively flat bottom (e.g., dF is 0.2D or less) can have a relatively small amount of backscattered light and can preferably scatter light forward into a relatively narrow angle. Thus, such a dot can provide a lens with less conspicuousness and higher therapeutic effect.

[0100] Generally speaking, the shape of a spot formed on a lens surface such as described above can be determined using conventional surface measurement techniques, such as SEM microscopy, optical interferometry, etc., and conventional image analysis techniques for extracting dimensions from images obtained using the measurement techniques.

[0101] As previously discussed, the spot shape for a surface point is defined by the shape of the perimeter in addition to the cross-sectional profile(s). In general, a spot can be formed with any perimeter shape, depending on the resolution of the method used to form the spot. In general, if a spot is formed using a method that involves depositing, removing, or modifying material at the lens surface, the spot can be formed by scanning a spot forming device, such as a laser (examples discussed below), along a path to alter the lens surface at that location and trace out the spot shape in the lens surface. The various path shapes used to form different spot perimeters are shown in FIG. Figure 4A-4S Depending on the resolution of the spot forming device and the size of the spot (e.g., width, as previously described), the spot forming device can be scanned along multiple paths, one within the other, to modify the lens surface of the entire spot. Figure 4A In a first example of the invention, point 401 has a five-pointed star peripheral shape. The point is formed by scanning the device along a first star-shaped path 401a and a second star-shaped path 401b inside path 401a.

[0102] Figure 4B A pear-shaped spot 402 is shown formed by tracking a spot forming device along a first path 402a and a second path 402b within the first path 402a.

[0103] Figure 4C A trapezoidal point 403 formed by a single path 403a is shown.

[0104] Figure 4D There is shown a path of points 404 formed by tracing the lens forming means along two elliptical paths 404a and two straight lines 404b.

[0105] Figure 4E An example of an octagonal spot 405 formed by scanning a spot forming device along a continuous piecewise spiral path 405a is shown. Figure 4FAnother example of a polygon of points formed by scanning a point forming device along a continuous piecewise spiral path 406a is shown. Figure 4G An example of an approximately circular spot 407 formed by scanning the spot forming device along a continuous spiral path 407a is shown.

[0106] Figure 4H A dumbbell shaped spot 408 is shown formed by tracking a spot forming device along a first path 408a and a second path 408b within the first path 408a.

[0107] Fig. 4I There is shown a trapezoidal dot 409 formed by tracking a dot forming device along a first path 409a and a second path 409b within the first path 409a.

[0108] Figure 4J A crescent-shaped spot 410 is shown formed by tracking a spot forming device along a first path 410a and a second path 410b within the first path 410a.

[0109] Figure 4K A zigzag shaped dot 411 is shown formed by tracking a dot forming device along a single closed path 411a.

[0110] Figure 4L A cat-head shaped dot 412 is shown formed by tracking a dot forming device along a first path 412a and a second path 412b within the first path 412a.

[0111] Figure 4M Another crescent-shaped spot 413 is shown formed by tracking the spot forming device along a first path 413a and a second path 413b within the first path 413a.

[0112] Figure 4N A conical spot 414a is shown formed by tracking a spot forming device along a first path 414a and a second path 414b within the first path 414a.

[0113] Fig.4O A polygon of points 415 is shown formed by tracking a point forming device along a series of hexagonal paths 415a.

[0114] Figure 4P A circular spot 416 is shown formed by tracking a spot forming device along a first path 416a and a second path 416b within the first path 416a. Both paths are circular.

[0115] Figure 4Q There is shown an elliptical spot 417 formed by tracking a spot forming device along a first path 417a and a second path 417b within the first path 417a. Both paths are elliptical.

[0116] Figure 4R A rectangular dot 418 is shown formed by tracking a dot forming device along a first path 418a and a second path 418b within the first path 418a. Both paths are rectangular.

[0117] Figure 4S There is shown a square dot 419 formed by tracking the dot forming device along a first path 419a, a second path 419b within the first path 419a, and a third path 419c within the second path 419b. Each path is square.

[0118] In general, any number of closed paths can be scanned in sequence to form dots of a desired shape and size. Other shapes are possible. Shapes that can be formed by scanning a dot-forming device along a single continuous path may be advantageous because they can be formed more efficiently (e.g., faster) than shapes formed by multiple separate paths. This is because a single continuous path generally avoids resetting the dot-forming device by moving the dot-forming device from one path to another.

[0119] The effect of spot size and shape on scattering can be studied by physical light scattering experiments and / or by optical computer simulations. Optical simulation software is used to model the forward and backscattering characteristics of scattering with simple geometries. For the purpose of simulation, eyeglass lenses with planar lens dimensions (front R 124 mm, rear R 123.2 mm, thickness 2 mm) and a model eye with the same dimensions as the human eye were modeled. Three fields of view of 0 degrees, 20 degrees and 40 degrees (full field of view) were used in the model to account for central, near peripheral and mid / far peripheral vision. In each case, all points were modeled on the back side of the lens (i.e., the surface facing the wearer).

[0120] The results of these simulations are Figure 5A and Figure 5B Here, Figure 5A The simulated number of light rays hitting the wearer's retina for five different clicks is shown. Figure 5B The number of simulated rays backscattered for the same five different points is shown. In each graph, the x-axis is the height or depth of the point, depending on whether the point is a protrusion or a depression.

[0121] Line 501 corresponds to the points formed by the hemispheric protrusions. Increasing the height of these protrusions does not significantly change the total amount of light hitting the retina, but it does change the distribution of forward and backscatter.

[0122] Line 502 corresponds to the hemispheric concavity. Ray tracing shows that the hemisphere with the smallest depth (10 μm) provides the greatest forward scatter and the least backscatter to the retina. Increasing the depth of the hemisphere reduces the light hitting the retina and increases backscatter. The analysis shows that the trend is not linear, i.e., at a depth of ~50 μm, there is no further reduction in forward scatter and at a depth of ~70 μm, there is no further increase in backscattered light.

[0123] Line 503 corresponds to a depression shaped like a hemisphere with concave ends. Ray tracing shows that the concave hemisphere with the smallest depth (10 μm) provides the greatest forward scattering and the least backscattering to the retina. Increasing the depth of the hemisphere reduces the light hitting the retina and increases backscattering. The greatest increase in backscattering occurs between 40 μm and 60 μm depth, and a sharp drop in forward scattering occurs between 10 μm and 30 μm depth. The analysis shows that at a depth of ~50 μm, there is no further significant reduction in forward scattering, and at a depth of ~60 μm, there is no further increase in backscattered light.

[0124] Line 504 corresponds to a depression shaped like an elongated hemisphere in the direction of the lens axis. Ray tracing shows that the hemisphere with the smallest Z height (50 μm) provides the greatest forward scatter and the least backscatter to the retina. Increasing the Z-direction hemisphere length reduces the light hitting the retina and increases backscatter; however, the rate of change is significantly smaller than that found by adjusting the hemisphere depth.

[0125] Line 505 corresponds to a concave shape like an elongated hemisphere with concave ends. Ray tracing shows that the elongated concave hemisphere with the smallest height (50 μm) provides the greatest forward scattering and the least backscattering to the retina. Increasing the length of the concave hemisphere reduces the light hitting the retina. Increasing the length of the concave hemisphere from 50 μm to 170 μm does not significantly change the backscattering, however, the backscattering increases dramatically from a height of 170 μm to 240 μm.

[0126] Based on simulations, both the "Hemisphere" and "Hemisphere with concave end" show the same trend of decreasing forward scattered light and increasing back scattered light with increasing depth. In both the "Hemisphere" and "Concave Hemisphere", the elongation of the scatterer in the Z direction does not seem to have much effect on both forward and back scattering. However, for hits, while a reasonable amount of light hits the retina at all depths, the back scattered light is also high. For larger hits, ray tracing shows that the impact on vision is minimal because forward scattering is minimal. The 20μm-30μm range achieves a balance between light scattering and contrast sensitivity for the protrusion.

[0127] In some examples, the dots can be designed to provide reduced narrow angle scatter and increased wide angle scatter to create a uniform light distribution on the retina / low contrast signal while maintaining acuity through the geometry of the scattering center. For example, the dots can be designed to generate significant wide forward angle scatter (e.g., such as more than 10%, 20% or greater, 30% or greater, 40% or greater, 50% or greater, deflected more than 2.5 degrees). Narrow angle forward scatter, i.e., within 2.5 degrees, can be kept relatively low (e.g., 50% or less, 40% or less, 30% or less, 20% or less).

[0128] As described above, dots can be formed on or in a lens (eg, an off-the-shelf lens) by adding material to the lens, removing material from the lens, and / or by changing the optical properties of the lens material.

[0129] In some examples, dots are formed on a lens surface or within a bulk material of the lens 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 create the dots. In general, a laser can be used to form dots on a lens surface or bulk material of the lens. For example, exposing a lens surface to a laser beam having sufficient energy can create dots by leaving small depressions and / or rough patches on the surface. By selectively exposing areas of the lens surface to laser radiation, a pattern of dots can be formed on the surface. For example, when the beam is pulsed, the laser beam can move relative to the surface. The relative motion between the beam and the lens surface may be caused by moving the beam while keeping the surface fixed, moving the surface while keeping the beam fixed, or moving both the beam and the surface.

[0130] Typically, the optical properties of a spot formed on a lens surface using a laser can be affected in several ways. For example, the energy density of the laser beam pulses can typically affect the physical and / or chemical interaction of the laser with the lens material. For example, for certain pulse energies, the lens material can melt at the exposed locations to form the spot. At some pulse energies, the spot can be formed by bubbling the lens material. This may occur at higher energies relative to melting of the lens. For some pulse energies, the interaction between the laser and the lens material can result in a color change in the lens material (e.g., by carbonization). In other cases, the lens material can be removed from the lens surface by ablation.

[0131] Other laser parameters can also affect the properties of the dots formed using the laser. These include laser wavelength, exposure time (e.g., how long each dot location is exposed), and number of passes (e.g., exposing an area multiple times with other areas exposed between each pass), each of which can be selected to achieve the desired surface modification. In addition, the interaction between the laser and the lens material will depend on the lens material itself. For example, dots in a lens material having a lower glass transition temperature can be formed using lower pulse energies or fewer pulses than dots in a lens material having a relatively higher glass transition temperature.

[0132] The resolution of the laser beam at the lens surface can be smaller than the desired spot size. For example, the beam resolution (e.g., as determined by the FWHM of the intensity distribution) can be about 50% or less (e.g., about 25% or less, about 10% or less, about 5% or less, about 1% or less) of the spot size. In some embodiments, the beam can form features that are 100 μm or less (e.g., 50 μm or less, 20 μm or less, 10 μm or less, 5 μm or less). In this case, the laser can be used to form spots with complex peripheral shapes and / or maximum widths that are significantly larger than the focused spot size, but doing so involves scanning the laser over a path to form the spot.

[0133] See also Figure 6 , a laser system 600 for forming a spot on a lens surface includes a laser 620, a beam chopper 630, a focusing optic 640, a mirror 650, and a stage 670. The laser 620 directs a laser beam toward the mirror 650, and the mirror 650 deflects the beam toward the lens 601, which 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.

[0134] A beam chopper 630 and focusing optics 640 are located in the beam path. Chopper 630 periodically blocks the beam so that lens 601 is exposed to discrete laser pulses. Focusing optics 640, which typically include one or more opto-dynamic elements (e.g., one or more lenses), focuses the beam to a sufficiently small spot on the surface of lens 601 so that the area ablated by the beam on the lens surface corresponds to the desired spot size. Actuator 660 changes the orientation of mirror 650 relative to the beam to scan the pulsed beam to different target points on the lens surface. Controller 610 coordinates the operation of laser 620, chopper 630, and actuator 660 so that the laser system forms a predetermined spot pattern on the lens.

[0135] In some embodiments, 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 orthogonal to the direction of beam propagation. Alternatively, or in addition, the actuator can move the stage in the direction of the beam. Moving the stage in the direction of the beam can be used to keep the exposed portion of the lens surface at the focal position of the beam, regardless of the curvature of the lens surface, thereby maintaining a substantially constant spot size across the lens surface. The stage actuator can also be controlled by the controller 610, which coordinates the stage motion with other elements of the system. In some embodiments, a stage actuator is used instead of a mirror actuator.

[0136] Typically, the laser 620 can be any type of laser that can generate light with sufficient energy to change the lens material (e.g., a batch of lens materials or coatings) to form a point. The laser can have a wavelength in the ultraviolet, visible, or infrared portion of the electromagnetic spectrum. Gas lasers, chemical lasers, dye lasers, solid-state lasers, and semiconductor lasers can be used. In some embodiments, an infrared laser, such as a CO2 laser (whose emission wavelength is 9.4 μm or 10.6 μm) can be used. A commercial laser system can be used, for example, a CO2 laser system manufactured by Universal Laser Systems, Inc. (Scottsdale, Arizona) (e.g., a 60W VLS 4.60 system). In some embodiments, a femtosecond laser can be used. For example, a commercial femtosecond laser system, such as a laser system manufactured by Trumpf (Santa Clara, California) (e.g., a TruMicro 2030 laser device as a TruLaser Station 5005) can be used to form a dot pattern of a desired shape and size. The burst mode of this laser device can achieve a burst energy much higher than the maximum energy of a single pulse, resulting in a higher ablation rate. This exemplary laser system can provide a pulse duration of less than 400 femtoseconds and a maximum pulse energy of 50 μJ.

[0137] The pulse duration and pulse energy are generally selected to provide a spot of a desired size. For example, in some embodiments, the laser 620 forms a predetermined dot pattern on the lens 601 by melting material at the surface of the lens 601. For example, the laser 620 heats and melts a portion of the surface of the lens 601 to form a predetermined pattern because the laser etching expands the melted material of the lens 601, resulting in raised marks forming a predetermined dot pattern.

[0138] In some embodiments, the laser 620 uses laser foaming to form a predetermined dot pattern on the lens 601. For example, the laser 620 uses laser foaming to melt the polymer material and attach it to the lens 601, where the laser 620 marks the foaming to form the predetermined dot pattern.

[0139] In some examples, the laser 620 forms a predetermined dot pattern on the lens 601 using a laser marker. For example, the laser marker forms the 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 of a portion of the lens 601 that forms the predetermined dot pattern. In another example, the laser 620 forms the predetermined dot pattern on the lens 601 by burning the lens 601 using the laser marker to form the predetermined dot pattern on the lens 601.

[0140] In some embodiments, laser 620 uses ablation to form a predetermined dot pattern on lens 601. For example, laser 620 is used to ablate (e.g., remove material) lens 601 to form a predetermined dot pattern by evaporating or sublimating lens 601. After ablation, pits may be formed on lens 601.

[0141] In some examples, to reduce the conspicuity of the dot pattern (e.g., to reduce backscattering and reflections due to the ablation pits at the scattering centers), the surface of the ablation pits on the lens 601 is modified to reduce the surface roughness (e.g., creating a dot with a larger bottom size relative to the dot size and a small dF relative to the depth of the dot). Reducing the surface roughness can reduce the effects of small angle light scattering (e.g., where the scattering angle is less than 3 degrees). For example, the surface of the ablation pits on the lens 601 can be modified by a second pass ablation to melt the rough surface of the ablation pit (e.g., by using lower energy ablation). Lower energy ablation can be achieved, for example, by defocusing the laser 620 (e.g., by increasing the beam width of the laser 620). In some embodiments, continuing to reduce the conspicuity of the dot pattern involves defocusing the laser 620 in multiple iterations. For example, the defocusing laser 620 undergoes an increase in defocus (e.g., increasing the beam width each time through) over several passes (e.g., every second, third, fourth, etc. ablation pass) to affect the taper of the pit (e.g., feathering or smoothing the pit edge). In some embodiments, reducing the conspicuity of the dot pattern involves performing multiple overlapping ablations to form an ablation crater having multiple overlapping ablation craters.

[0142] In some embodiments, reducing the conspicuity of the dot pattern involves coating the back side of lens 610 with an anti-reflective layer. In some embodiments, a reflective layer is coated on the front surface of the lens. This is particularly beneficial if laser ablation is performed on the back side of lens 601. Typically, the laser 620 has a greater effect on the coating than on the lens 601 material, thereby affecting the taper of the pits (e.g., feathering or smoothing of the pit edges).

[0143] exist Figure 7 and Figure 8 The example of two laser paths for forming a spot shown in FIG. 1 each has a width of 140 μm. Figure 7 The spot shapes formed by scanning two discrete paths 710 and 720 are shown. The outer path 710 is an octagon. The inner path, which is 75 μm wide, is a hexagon. Scanning these paths involves moving the laser from the first path to the second path without exposing the lens surface.

[0144] Figure 8 Shows the formation and Figure 7 The same octagonal segmented spiral path of the laser as shown in 810. However, here the dots are formed by tracking the laser along a single continuous path, so there is no need to move the laser from one path to the next to complete the formation of the dots. Such dots can be formed more quickly than dots involving more than one discrete path. In addition, such a path can produce dots with smoother bottoms than dots of similar size formed by scanning multiple discrete paths.

[0145] This is 9A to 9C and FIG. 10A to FIG. 10C It is obvious from the comparison of the points shown that they correspond to the use of Figure 8 and Figure 7 The two points formed by the path shown. In particular, 9A to 9C Show use as Figure 8 The spiral path shown in Figure 1 forms two points. Fig.9A A top view of a point obtained using optical interferometry is shown. Fig. 9B These points are similarly shown rendered in black and white. Fig. 9C A cross-sectional profile is shown starting from the section at one of the points.

[0146] Fig. 10A and Fig. 10B Shows the use of Figure 7 A top view of the three points formed by the dual paths shown. Fig. 10C A cross section through one of the points is shown, illustrating that the surface roughness is significantly higher at the bottom of one of the points.

[0147] These two examples are laser exposures, which involve continuously exposing the lens surface while the laser scans each discrete path. However, other exposure schemes are possible. For example, in some cases, the laser can be pulsed as it scans along the discrete paths. Fig.11A An example of this is shown, which shows a spiral path 1101. The laser is pulsed as it scans along path 1101, thereby producing multiple separate exposure areas. The winding of the spiral path relative to the focal spot size is tight enough that the exposure areas overlap along the path and also overlap with exposure areas in adjacent loops of the spiral. The result is a nearly circular spot with a relatively smooth bottom. In addition, this exposure scheme can result in a lower total laser dose being delivered to the lens area, resulting in a shallower spot than would be achieved using a single continuous exposure to form the spot.

[0148] Examples of dots formed using a spiral path and pulsed lasers are Figure 11B-Figure 11D shown. Fig. 11B and Fig. 11C A top view of three such points is shown, and Fig.11D A cross-sectional profile of one of the spots is shown. The spot depth is approximately 5 μm. The bottom roughness through this section is only slightly less than the depth, but considering how shallow the spot is, this is a relatively small roughness overall.

[0149] Laser formation of a dot can result in a phenomenon known as "burn-in," where the initial exposure location at the beginning of the laser path results in a portion of the dot that is darker than the rest of the dot. This burn-in can manifest as a groove on one side of the dot. The asymmetry created by this burn-in groove can result in asymmetric scattering of different portions of the dot. In some embodiments, for example, where burn-in is unavoidable, it may be desirable to symmetrically form the burn-in grooves at different locations of the dot to reduce asymmetric scattering. Additionally, the location of the burn-in grooves can be varied for different points on the lens to reduce the overall asymmetry of the scattering, or to control and exploit asymmetry across a reduced contrast region of the lens.

[0150] Now refer to Figure 12A-12C To describe such an example. Fig. 12A A plan view of lens 1200 is shown with a region of reduced contrast 1208 surrounding a clear aperture 1212. The region of reduced contrast 1208 includes dots 1216 arranged in a radial array pattern. Each dot 1216 includes a depression formed in a surface 1220 of lens 1200 using a symmetrical burn-in technique, resulting in two grooves on opposite sides of the dot.

[0151] like Fig. 12B and Fig. 12C, which respectively show a plan view of a portion of the contrast-reduced region 1208 and a cross section through one of the points. Each point 1216 includes a first sidewall 1224, a second sidewall 1128, and a central region 1132 between the sidewalls 1124 and 1128. Depth profile ( Fig. 12C ) shows the depression produced by burn-in of laser radiation during spot formation, which includes grooves 1136 and 1140 adjacent to sidewalls 1124 and 1128, respectively.

[0152] The first trench 1236 has a depth D1 that is substantially equal to a depth D2 of the second trench 1240. The central region 1232 is disposed between the first trench 1236 and the second trench 1240, and has a depth D3 that is less than the depth D1 of the first trench 1236 and the depth D2 of the second trench 1240.

[0153] As used herein, a "groove" may include a groove, channel, cavity or indentation having a depth greater than that of adjacent portions. Typically, the grooves on opposite sides of a point can have the same depth or different depths.

[0154] like Fig. 12B As shown, the width of the grooves is not constant around the perimeter of the dots. Instead, each groove is crescent-shaped, with the widest portion corresponding to section C and the narrowest portion passing through the section perpendicular to C. The orientation of the crescent-shaped grooves is aligned with the radial direction of the array of dots in the area of ​​reduced contrast 1208. This variation in groove alignment can provide increased overall uniformity of average light scattering across the area of ​​reduced contrast.

[0155] like Fig. 12C The varying depths of the depth profile shown can be formed in a variety of ways using laser burning. A first example method 1300 of forming a point 1316 having a symmetrical depth profile is shown in FIG. Fig.13As shown. In the method 1300, the laser exposure time at different locations of the point 1316 is controlled to produce a symmetrical burn-in depression. Initially, the first step 1304 of the method 1300 includes focusing the laser beam of the laser system. The second step 1308 of the 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 a new point 1216 is formed in the surface 1220 of the lens 1200, the laser exposes the lens surface 1220 to an initial burst of intense laser radiation, thereby producing an initial burn-in that defines a first sidewall 1224 and a first groove 1236 disposed inwardly relative to the first sidewall 1224. In a third step 1312, the method 1300 includes causing relative motion between the laser beam and the lens in a first direction M, away from the first groove 1236, while exposing the lens 1200 to the focused laser radiation. In some examples, the laser moves away from the first sidewall 1224 in the M direction relative to the lens 1200 to continue forming the remainder of the dot recess. As the laser moves in the M direction, the lens 1200 is continuously exposed to the focused laser radiation of the laser beam, producing a burn-in that defines a central region 1232 of the dot 1216. The laser beam intensity when forming the central region 1232 is weaker than the initial burst of laser radiation, and thus the depth D3 of the central region 1232 is less than the depth D1 of the first trench 1236.

[0156] In a fourth step 1316, the method 1300 includes exposing a second location of the ophthalmic lens to focused laser radiation to form a second sidewall 1228 and a second groove 1240 disposed inwardly relative to the second sidewall 1228 of the point 1216. Again, because the intensity of the laser is weaker than the initial burst of radiation, the laser is paused for a period of time to expose the second groove 1240 to sufficient radiation to produce a burn-in having a depth D2 substantially equal to the depth D1 of the first groove 1236. Thus, the lens 1200 is exposed to the laser beam at the second groove 1240 for a period of time that is greater than the initial exposure at the first groove 1236.

[0157] In some examples, the intensity of the laser beam is controlled to produce symmetrical burn-in depressions. In this example, the laser beam exposes lens 1200 to a first laser intensity to create first trench 1236 and exposes a different location of lens 1200 to the first laser intensity to create second trench 1240.

[0158] In some examples, the intensity and exposure time are controlled to produce symmetrical burned-in depressions. In another example, the laser exposure can be pulsed to produce short, intense bursts of laser radiation to form the first trench and the second trench of the dot before forming the central region.

[0159] In some cases, the dot pattern includes dots that are randomly displaced relative to a regular array. Introducing random displacements can reduce optical effects associated with regularly spaced scattering centers, such as starburst-like glare. For example, see https: / / www.slrlounge.com / diffraction-aperture-and-starburst-effects / , which illustrates the starburst effect associated with photography. Therefore, including random displacements in the dot pattern can provide a more comfortable experience for the user compared to a similar dot pattern with evenly spaced scattering centers. Alternatively, or in addition, randomization of the dot pattern can reduce optical effects (e.g., diffraction or interference effects) manifested in the reflected light, thereby reducing the visibility of the dot pattern to the observer.

[0160] See also Fig.14 , the example dot pattern 1400 includes an annular zone 1404 surrounding a clear aperture 1408. The annular zone has dots 1412 arranged in a pattern 1400, the pattern 1400 including a radial direction B and a circumferential direction C. Specifically, the dots 1412 are arranged along a plurality of radial arrays 1416 relative to the clear aperture 1408 and in spaces 1420 between different radial arrays 1416. Specifically, dots 1412A of a first size are arranged along the radial arrays 1416, and dots 1412B of a different size are arranged in the spaces 1420 between the radial arrays 1416. According to the pattern 1400, the dot size changes when moving along the circumferential direction C, and the dot size remains uniform when moving along the radial direction B.

[0161] The pattern 1400 also includes a second annular zone 1424 adjacent to the aperture 1408, wherein the dots 1412A are of a first size. In the second annular zone 1424, the dot size is constant in both the radial direction B and the circumferential direction C2. However, in other examples, the pattern 1400 may include only one annular zone or more than two annular zones having different patterns of dots.

[0162] Fig.15 1504. is another example dot pattern 1500 and includes an annular zone 1504 surrounding a clear aperture 1508. The annular zone 1504 has spaced dots 1512 arranged in a pattern including a radial direction E and a circumferential direction F. Specifically, the dots 1512 are arranged along a plurality of radial arrays 1516 relative to the aperture 1508 and in 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 spaces 1520 between the radial arrays 1516 within the first annular zone 1504. According to the pattern 1500, the dot size changes when moving along the circumferential direction F, and the dot size remains uniform when moving along the radial direction E.

[0163] The pattern 1500 also includes a second annular region 1524 adjacent to the aperture 1508, wherein the dots 1512A are of a first size. In the second annular region 1524, the size of the dots is uniform in both the radial direction E and the circumferential direction F2.

[0164] exist Fig.16 , another example dot pattern 1600 for an ophthalmic lens includes an annular contrast-reduced region 1604 surrounding a clear aperture 1608. The annular region 1604 has dots 1612 spaced apart to scatter incident light. The dots 1612 are arranged in a pattern including a radial direction G and a circumferential direction H. Specifically, a plurality of dots 1612 are arranged along a plurality of radial arrays 1616 relative to the aperture and in spaces 1620 between different radial arrays 1616. Dots 1612A of a first size are arranged along the radial arrays 1616, and smaller dots 1612B are arranged in spaces 1620 between the radial arrays 1616 within the first annular region 1604. According to the pattern 1600, the dot size changes when moving along the circumferential direction H, and the dot size remains uniform when moving along the radial direction G.

[0165] The pattern 1600 also includes a second annular area 1624 adjacent to the aperture 1608, wherein the third-sized dots 1612C are arranged between the first-sized dots 1612A. In the second annular area 1624, the size of the dots varies along the circumferential direction H2. The third-sized dots 1612C are arranged in different patterns, including irregular variations in the spacing between adjacent dots 1612A. In the example shown, the third-sized dots 1612C are randomly arranged between the radial arrays 1616. However, in other examples, the third-sized dots 1612C (e.g., smaller than dots 1612A and 1612B) can be evenly spaced between adjacent dots 1612A, 1612C. In yet another example, the second-sized dots 1612B can also be arranged adjacent to the dots 1612A, 1612C of other sizes.

[0166] Although relative to Fig. 12A , Fig.14 , Fig.15 and Fig.16 The aforementioned example dot patterns described are each composed of spaced-apart dots, but patterns with overlapping dots are also possible. Fig.17, the example dot pattern 1700 includes an annular contrast-reduced region 1704 surrounding a clear aperture 1708, and overlapping dots 1712 to scatter incident light in the annular region 1704. The dots 1712 are arranged in a random pattern 1700 and are uniform in size. In some cases, one dot overlaps another dot, while in other cases, one dot overlaps two or more other dots. The dots 1712 may simply touch or overlap each other to varying degrees (e.g., overlapping by about 1% to about 99% in dot surface area). For example, point overlap (determined by the percentage of the area of ​​a point that overlaps with one or more other points) can be 5% or greater (e.g., 10% or greater, 15% or greater, 20% or greater, 25% or greater, 30% or greater, 35% or greater, 40% or greater, 45% or greater, 50% or greater, 55% or greater, 60% or greater, 65% or greater, 70% or greater, 75% or greater, 80% or greater, 85% or greater, 90% or greater, 95% or greater).

[0167] Fig.18 1 is another example dot pattern 1800 that includes an annular contrast-reduced region 1804 surrounding a clear aperture 1808, and overlapping dots 1812 for scattering light in the contrast-reduced region. The dot pattern 1800 includes a grid of vertical rows 1814 and columns 1818. In the example shown, dots 1812 arranged in a row 1814 overlap with adjacent dots 1812 in the same row 1814. However, dots 1812 in a column 1818 do not overlap with adjacent dots 1812 in the same column 1818. Multiple dots 1812 may simply touch or overlap each other to varying degrees (e.g., overlapping by area from about 1% to about 99%).

[0168] exist Fig.19 , another example dot pattern 1900 includes dots 1912 in an annular reduced contrast region 1904 surrounding a clear aperture 1908 to scatter incident light in the reduced contrast region. The dot pattern 1900 includes a grid of rows 1914 and columns 1918, wherein dots 1912 arranged in rows 1914 overlap with adjacent dots 1912 in the same row 1914, and dots 1912 arranged in columns 1918 overlap with adjacent dots 1912 in the same column 1918. In the example shown, 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 (e.g., row 1914B, column 1918B), some dots 1912 overlap with adjacent dots 1912 in the same column 1918 and the same row 1914. Multiple dots 1912 may simply touch or overlap each other to varying degrees (e.g., overlapping by area from about 1% to about 99%).

[0169] like Fig. 20 As shown, yet another example dot pattern 2000 for an ophthalmic lens includes a contrast-reduced area consisting of a first annular zone 2004 and a second annular zone 2024 surrounding a clear aperture 2008, and overlapping dots 2012 to scatter incident light in the contrast-reduced areas 2004, 2024. The dot pattern 2000 includes a plurality of dots arranged in radial directions and circumferential directions relative to the aperture 2008. Specifically, the plurality of dots 2012 are arranged to overlap along a plurality of radial arrays 2016 relative to the aperture 2008 and in spaces 2020 between different radial arrays 2016. A plurality of dots 2012A of a first size are arranged in the two annular zones 2004, 2024 along the radial arrays 2016, and a plurality of dots 2012B of different sizes are disposed in the spaces 2020 between the radial arrays 2016 and within the first annular zone 2004. Pattern 2000 also includes a second annular region 2024 adjacent to aperture 2008, wherein point 2012A is of a first size. In some cases, point 2012 overlaps adjacent points of the same and / or different sizes. In some cases, one point 2012 overlaps another point 2012, and in other cases, overlaps two or more other points 2012. Multiple points 2012 may simply touch or overlap each other to varying degrees (e.g., from about 1% to about 99% overlap). In other cases, point 2012 does not overlap any other point 2012.

[0170] exist Fig.21 In another example, a dot pattern 2100 for an ophthalmic lens includes a contrast-reduced area having a first annular zone 2104 and a second annular zone 2124 surrounding a clear aperture 2108, and dots 2112 in the first annular zone 2104 and the second annular zone 2124. In the first annular zone 2104, some dots 2112 of different sizes overlap with adjacent dots 2112 of the same or different sizes. In the second annular zone 2124, the dots 2112 are uniform in size and do not overlap with adjacent dots 2112. In some cases, the dots 2112 overlap with adjacent dots 2112 of the same and / or different sizes. In some cases, one dot 2112 overlaps with another dot 2112, and in other cases, overlaps with two or more other dots 2112. The plurality of overlapping dots 2112 may simply touch or overlap each other to varying degrees (e.g., overlapping by area from about 1% to about 99%).

[0171] Fig. 22Another example dot pattern 2200 for an ophthalmic lens is shown, which includes a contrast-reduced area having a first annular zone 2204, a second annular zone 2224, and a third annular zone 2228. The third annular zone 2228 surrounds the clear aperture 2208 and has overlapping dots 2212 of different sizes 2212A, 2212B, 2212C arranged in a random pattern. In some cases, the dots 2212 overlap with adjacent dots 2212 of the same and / or different sizes. The dots 2212 in the second annular zone 2224 do not overlap, and the dots 2212 in the third annular zone 2228 overlap with one or more adjacent dots 2212. In some cases, one dot 2212 in the first annular zone 2204 and the third annular zone 2228 overlaps with another dot 2212, and in other cases, overlaps with two or more other dots 2212. The plurality of overlapping dots 2212 may simply touch or overlap each other to varying degrees (e.g., overlapping by area by about 1% to about 99%).

[0172] In some examples, the dot pattern is characterized by a gradient, e.g., dot size and / or spacing. The dot pattern can be characterized by a gradient in the scattering efficiency of the dots (e.g., due to a refractive index mismatch and / or a gradient in the shape of each dot). A gradient dot pattern can reduce the conspicuity of the pattern. For example, a gradual transition from a clear portion of a lens to a scattering portion may be less noticeable than a sharp transition.

[0173] In addition to the embodiments and embodiments of the appended claims above, the following numbered embodiments are also innovative.

[0174] Embodiment 1 is an ophthalmic lens, comprising: a lens body having a pair of relative curved surfaces; a plurality of discrete light scattering centers arranged in the region of at least one relative curved surface, each scattering center having a shape at least partially defined by a peripheral shape, a maximum depth D, and a maximum width W, wherein a ratio of D / W is 1 / 5 or less.

[0175] Embodiment 2 is an ophthalmic lens, comprising: a lens body having a pair of relative curved surfaces; a plurality of discrete light scattering centers arranged in the region of at least one of the relative curved surfaces, each scattering center having a shape at least partially defined by a peripheral shape, a maximum depth D, and a maximum width W, wherein D is 20 micrometers (μm) or less, and W is 100 μm or greater.

[0176] Embodiment 3 is an ophthalmic lens, comprising: a lens body having a pair of opposite curved surfaces defining a lens axis; a plurality of discrete light scattering centers arranged in a region of at least one of the opposite curved surfaces, each scattering center having a concavity having a maximum depth D and a maximum width W, and a concavity having a minimum width W. floor and the maximum depth change δD floor The bottom of the floor is 0.5W or greater, and δDfloor 0.2D or less.

[0177] Embodiment 4 is an ophthalmic lens, comprising: a lens body having a pair of relative curved surfaces defining a lens axis; a plurality of discrete light scattering centers arranged in the region of at least one of the relative curved surfaces, each scattering center having a shape at least partially defined by a peripheral shape, a maximum depth, and a maximum width, wherein the peripheral shape is selected from the group consisting of a star, a regular polygon, a dumbbell, a pear, a parallelogram, a crescent, a cone, and a sawtooth.

[0178] Embodiment 5 is an ophthalmic lens, comprising: a lens body having a pair of relative curved surfaces; a plurality of discrete light scattering centers are arranged in an area of ​​at least one relative curved surface, wherein the density of the light scattering centers in the area and the shape of the light scattering centers are selected so that for light incident on an area of ​​the lens propagating parallel to the axis of the lens, the ophthalmic lens backscatters 12% or less of the light incident on the area, and forward scatters other light incident on the area, and 50% or more of the forward scattered light is forward scattered into a solid angle of 5 degrees.

[0179] The ophthalmic lens of Embodiment 6 and any of the preceding embodiments, wherein the region surrounds a clear region lacking scattering centers.

[0180] Embodiment 7 is the ophthalmic lens of any of the preceding embodiments, wherein the region is an annular zone.

[0181] Embodiment 8 is the ophthalmic lens of any of the preceding embodiments, wherein the light scattering centers are formed on a single surface of the ophthalmic lens.

[0182] Embodiment 9 is the ophthalmic lens of any of embodiments 1-7, wherein light scattering centers are formed only on a single surface of the ophthalmic lens.

[0183] Embodiment 10 is the ophthalmic lens of embodiment 9, wherein the single surface is concave.

[0184] Embodiment 11 is the ophthalmic lens of embodiment 9, wherein the single surface is convex.

[0185] Embodiment 12 is the ophthalmic lens of any of the preceding embodiments, wherein each scattering center has the same shape.

[0186] Embodiment 13 is the ophthalmic lens of any of embodiments 1-11, wherein at least some of the scattering centers have different shapes.

[0187] Embodiment 14 is the ophthalmic lens of any one of the preceding embodiments, wherein the ophthalmic lens is a spectacle lens or a contact lens.

[0188] Embodiment 15 is the ophthalmic lens of any one of the preceding embodiments, wherein the ophthalmic lens is a planar lens, a single vision lens, or a multifocal lens.

[0189] Embodiment 16 is a method comprising: exposing a surface of an ophthalmic lens to one or more pulses of laser radiation sufficient to produce light scattering centers on the surface; and moving the laser radiation relative to the surface while exposing the surface to trace a path on the surface, wherein the path has a spiral shape and the light scattering centers have a maximum width W in the range of 100 microns to 1,000 microns.

[0190] Embodiment 17 is a method comprising: exposing a surface of an ophthalmic lens to one or more pulses of laser radiation sufficient to produce light scattering centers on the surface; and moving the laser radiation relative to the surface while exposing the surface to trace a path on the surface, wherein the light scattering centers have a maximum width W in the range of 100 microns to 1,000 microns and a peripheral shape selected from the group consisting of a star, a regular polygon, a dumbbell, a pear, a parallelogram, a crescent, a cone, and a sawtooth.

[0191] Embodiment 18 is an ophthalmic lens, comprising: a lens body having two relative surfaces; and an annular zone surrounding a clear aperture, wherein the annular zone has a plurality of light scattering centers in the lens body and / or on at least one of the two relative surfaces, which are sized and shaped to scatter incident light, wherein a first light scattering center of the plurality of light scattering centers overlaps with an adjacent light scattering center.

[0192] Embodiment 19 is the ophthalmic lens of embodiment 18, wherein the light scattering centers are arranged in a pattern comprising rows, wherein a first light scattering center and an adjacent light scattering center are arranged in a row.

[0193] Embodiment 20 is the ophthalmic lens of embodiment 19, wherein the light scattering centers are arranged in a pattern comprising columns.

[0194] Embodiment 21 is the ophthalmic lens of embodiment 20, wherein the second light scattering center overlaps with the third light scattering center in a column.

[0195] Embodiment 22 is the ophthalmic lens of embodiment 20 or 21, wherein the first light scattering center overlaps with the different light scattering center, and the first scattering center and the different light scattering center are arranged in a column.

[0196] Embodiment 23 is the ophthalmic lens of embodiment 18, wherein a first light scattering center is a first size and an adjacent light scattering center is a second size different than the first size.

[0197] Embodiment 24 is the ophthalmic lens of embodiment 18, wherein the light scattering centers are arranged in a pattern that includes a circumferential direction and a radial direction relative to the clear aperture.

[0198] Embodiment 25 is the ophthalmic lens of embodiment 18, wherein the light scattering centers are arranged in a pattern that includes irregular variations in spacing between adjacent light scattering centers.

[0199] Embodiment 26 is the ophthalmic lens of any one of embodiments 18 to 25, comprising a second annular zone, wherein the light scattering centers disposed in the second annular zone do not overlap.

[0200] Embodiment 27 is the ophthalmic lens of embodiment 18, wherein the lens has a lens axis and the aperture and the annular zone are substantially centered about the lens axis.

[0201] Embodiment 28 is an ophthalmic lens, comprising: a lens body having two opposing surfaces; and an annular zone surrounding a clear aperture, wherein the annular zone has a plurality of spaced-apart light scattering centers on at least one surface of the lens body and / or the two opposing surfaces, which are sized and shaped to scatter incident light, and the light scattering centers are arranged in a pattern including a circumferential direction and a radial direction relative to the clear aperture, wherein the light scattering centers arranged in the radial direction have a first size, and the light scattering centers arranged in the circumferential direction have a second size different from the first size.

[0202] Embodiment 29 is the ophthalmic lens of embodiment 28, wherein the first dimension is uniform and the second dimension is variable.

[0203] Embodiment 30 is the ophthalmic lens of embodiment 28, comprising a second annular zone disposed between the clear aperture and the annular zone, wherein the light scattering centers disposed in the second annular zone are uniform in size in both radial and circumferential directions.

[0204] Embodiment 31 is the ophthalmic lens of embodiment 28, wherein a portion of the light scattering centers are arranged in a different pattern including irregular variations in the spacing between adjacent light scattering centers.

[0205] Embodiment 32 is the ophthalmic lens of embodiment 28, wherein the light scattering centers are substantially circular.

[0206] Embodiment 33 is the ophthalmic lens of embodiment 28, wherein the lens has a lens axis and the aperture and the annular zone are substantially centered about the lens axis.

[0207] Example 34 is the ophthalmic lens of Example 28, wherein the lens is a spectacle lens or a contact lens.

[0208] Embodiment 35 is an ophthalmic lens, comprising: a lens body having two opposing surfaces; and an annular zone surrounding a clear aperture, wherein the annular zone has a plurality of spaced-apart light scattering centers on at least one surface of the lens body and / or the two opposing surfaces, which are sized and shaped to scatter incident light, and the light scattering centers are arranged in a pattern including a circumferential direction and a radial direction relative to the clear aperture, wherein the light scattering centers arranged in the radial direction have a uniform size, and the light scattering centers arranged in the circumferential direction have different sizes.

[0209] Embodiment 36 is the ophthalmic lens of embodiment 35, comprising a second annular zone disposed between the clear aperture and the annular zone, wherein light scattering centers disposed in the second annular zone are uniform in size in radial and circumferential directions.

[0210] Embodiment 37 is the ophthalmic lens of embodiment 28, wherein a portion of the light scattering centers are arranged in a different pattern including irregular variations in the spacing between adjacent light scattering centers.

[0211] Embodiment 38 is an ophthalmic lens, comprising: a lens body having two opposing surfaces; and an annular zone surrounding a clear aperture, wherein the annular zone has a plurality of spaced-apart light scattering centers on at least one of the two opposing surfaces, which are sized and shaped to scatter incident light, each light scattering center comprising a depression in the surface, wherein one or more light scattering centers have a depth profile relative to the surface, the profile comprising a first groove positioned toward a first sidewall of the depression and a second groove positioned toward a second sidewall of the depression.

[0212] Embodiment 39 is the ophthalmic lens of embodiment 38, wherein the depth profile of the concavity is symmetric about at least one plane.

[0213] Embodiment 40 is the ophthalmic lens of embodiment 38, wherein the depth profile of the concavity is axisymmetric.

[0214] Embodiment 41 is the ophthalmic lens of embodiment 38, wherein the maximum depth of the first grooves is substantially equal to the maximum depth of the second grooves.

[0215] Embodiment 42 is the ophthalmic lens of embodiment 41, wherein the region between the first groove and the second groove of the one or more light scattering centers has a depth different from the maximum depth of the first groove and the maximum depth of the second groove.

[0216] Embodiment 43 is the ophthalmic lens of Embodiment 38, wherein the orientation of the grooves in different ones of the light scattering centers varies at different locations of the annular zone.

[0217] Embodiment 44 is the ophthalmic lens of any one of embodiments 38 to 43, wherein the one or more light scattering centers have a circular peripheral shape.

[0218] Embodiment 45 is the ophthalmic lens of any one of embodiments 38 to 44, wherein the maximum width of the light scattering centers is in a range of 100 micrometers (μm) to 1,500 μm.

[0219] Embodiment 46 is the ophthalmic lens of any one of Embodiments 38 to 45, wherein the radial dimension of the first groove is 0.3W or less, wherein W is the maximum width of the light scattering center.

[0220] Embodiment 47 is the ophthalmic lens of any one of embodiments 38 to 46, wherein the depth profile comprises one or more additional grooves between the first groove and the second groove.

[0221] Embodiment 48 is a method comprising: exposing a first position of an ophthalmic lens of a lens material to focused laser radiation of a laser beam to form a first sidewall of an optical scattering feature on a surface of the ophthalmic lens; causing relative movement between the laser beam and the lens in a first direction away from the first sidewall while exposing the lens to the focused laser radiation; and exposing a second position of the ophthalmic lens to the focused laser radiation to form a second sidewall of the optical scattering feature, wherein exposing the first position and the second position of the lens produces a depression in the lens material having a depth profile relative to the surface of the ophthalmic lens, the depth profile comprising a first groove positioned toward the first sidewall and a second groove positioned toward the second sidewall.

[0222] Embodiment 49 is the method of embodiment 48, wherein exposing the first position comprises exposing the first position of the lens for a first time period, and wherein exposing the second position comprises exposing the second position for a second time period greater than the first time period.

[0223] Embodiment 50 is the method of embodiment 48 or 49, wherein the first sidewall and the second sidewall form circular optical scattering features.

[0224] Embodiment 51 is the method of any one of Embodiments 48 to 50, wherein a depth of the first trench is substantially equal to a depth of the second trench.

[0225] Embodiment 52 is the method of any one of Embodiments 48 to 51, wherein causing the relative motion creates a region between the first groove and the second groove at one or more points, the depth of the region being different from the depth of the first groove and the depth of the second groove.

[0226] Embodiment 53 is an ophthalmic lens comprising: a lens body having two opposing surfaces; and an annular zone surrounding a clear aperture, wherein the annular zone has a plurality of light scattering centers in the lens body and / or on at least one of the two opposing surfaces, which are sized and shaped to scatter incident light, wherein at least some of the plurality of scattering centers have diameters in the range of approximately 1.001 mm to approximately 1.5 mm, and the spacing between the points varies across the annular zone.

[0227] Embodiment 54 is the ophthalmic lens of embodiment 53, wherein the light scattering centers are arranged in a pattern including a circumferential direction and a radial direction relative to the clear aperture, wherein the light scattering centers arranged along the radial direction have a uniform size and the scattering centers arranged along the circumferential direction have a variable size.

[0228] Embodiment 55 is the ophthalmic lens of Embodiment 53, comprising a second annular zone disposed between the clear aperture and the annular zone, wherein the light scattering centers disposed in the second annular zone are uniform in size in both radial and circumferential directions.

[0229] Embodiment 56 is the ophthalmic lens of embodiment 53, wherein a first light scattering center of the plurality of light scattering centers overlaps with an adjacent light scattering center.

[0230] Embodiment 57 is the ophthalmic lens of embodiment 56, wherein the light scattering centers are arranged in a pattern comprising rows, wherein a first light scattering center and an adjacent light scattering center are arranged in a row.

[0231] Embodiment 58 is the ophthalmic lens of embodiment 57, wherein the light scattering centers are arranged in a pattern comprising columns.

[0232] Embodiment 59 is the ophthalmic lens of embodiment 53, wherein the light scattering centers are arranged in a pattern that includes irregular variations in spacing between adjacent scattering centers.

[0233] Embodiment 60 is the ophthalmic lens of embodiment 53, wherein each light scattering center comprises a depression in one of the surfaces of the ophthalmic lens, wherein one or more light scattering centers have a depth profile relative to the surface of the ophthalmic lens, the depth profile comprising a first groove positioned toward a first side wall of the light scattering center and a second groove positioned toward a second side wall of the light scattering center.

[0234] Embodiment 61 is the ophthalmic lens of embodiment 60, wherein the depth profile of one or more light scattering centers is symmetrical.

[0235] Embodiment 62 is the ophthalmic lens of embodiment 60, wherein the depth of the first groove is substantially equal to the depth of the second groove.

[0236] Although this specification contains many specific implementation details, these details should not be interpreted as limitations on the scope of any disclosure or what may be claimed, but rather as descriptions of features that may be specific to a particular disclosed particular example. Certain features described in this specification in the context of separate examples may also be implemented in combination in a single example. Conversely, various features described in the context of a single example may also be implemented separately in multiple examples, or in any suitable sub-combination. In addition, although features may be described herein as working in certain combinations and even initially claimed as such, one or more features from the claimed combination may be removed from the combination in some cases, and the claimed combination may point to a sub-combination or a variation of the sub-combination.

[0237] Similarly, although operations are described in a particular order in the accompanying drawings, this should not be understood as requiring that such operations be performed in the particular order or sequential order shown, or that all of the operations shown be performed, in order to achieve the desired results. In some cases, multitasking and parallel processing may be advantageous. In addition, 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.

[0238] Specific examples of the subject matter have been described. Other examples are within the scope of the appended claims. For example, the actions recited in the claims can be performed in a different order and still achieve the desired results. As an example, the processes described in the accompanying drawings do not necessarily require the particular order or sequential sequence shown to achieve the desired results. In some embodiments, multitasking and parallel processing may be advantageous.

Claims

1. An ophthalmic lens comprising: A lens body having two opposite curved surfaces; as well as a region having a plurality of light scattering centers in the lens body and / or on at least one of the two opposing curved surfaces, Features: The light scattering centers are sized and shaped so as to scatter incident light, the region corresponding to the peripheral field of vision of a user of the ophthalmic lens, Wherein, at least some of the plurality of light scattering centers have diameters in a range of 1.001 mm to 1.5 mm, and spacing between the light scattering centers varies across the annular region.

2. The ophthalmic lens according to claim 1, wherein: The light scattering centers are arranged in a pattern including a circumferential direction and a radial direction relative to the center of the lens body, Wherein, the light scattering centers arranged along the radial direction have uniform sizes, and the light scattering centers arranged along the circumferential direction have variable sizes.

3. The ophthalmic lens according to claim 1, wherein: All of the light scattering centers have diameters ranging from 1.001 mm to 1.5 mm.

4. The ophthalmic lens according to claim 1, wherein: A first light scattering center among the plurality of light scattering centers overlaps with an adjacent light scattering center.

5. The ophthalmic lens according to claim 4, wherein: The light scattering centers are arranged in a pattern comprising rows, wherein the first light scattering center and adjacent light scattering centers are arranged in the rows.

6. The ophthalmic lens according to claim 5, wherein: The light scattering centers are arranged in a pattern comprising columns.

7. The ophthalmic lens according to claim 1, wherein: The light scattering centers are arranged in a pattern including irregular variations in spacing between adjacent light scattering centers.

8. The ophthalmic lens according to claim 1, wherein: each of the light scattering centers comprises a depression in one of the surfaces of the ophthalmic lens, Wherein, one or more of the light scattering centers have a depth profile relative to the one surface of the ophthalmic lens, and the depth profile includes a first groove positioned toward a first side wall of the light scattering center and a second groove positioned toward a second side wall of the light scattering center.

9. The ophthalmic lens according to claim 8, wherein: The depth profile of the one or more light scattering centers is symmetrical.

10. The ophthalmic lens according to claim 8, wherein: The depth of the first trench is equal to the depth of the second trench.

11. A pair of glasses, characterized in that Comprising the ophthalmic lens of claim 1.

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