Ophthalmic lens for influencing myopia progression and method for designing lens thereof

Abstract

The present disclosure relates to a myopia control lens comprising a vertical power profile distribution defining a vertical channel extending along a vertical meridian of an ophthalmic lens to at least one of a bottom boundary and a top boundary of the ophthalmic lens, the vertical channel being substantially free of distortion, thus, a substantially clear viewing area is generated. This allows the wearer to simply guide his natural eye without adjusting the head and posture for focusing, thereby enabling near vision focusing at the comfortable natural posture of the wearer. The lenses of the present disclosure may be integrated into framed eyeglasses, or may be configured as contact lenses.

Description

Technical Field

[0001] Embodiments of the presently disclosed subject matter relate generally to optical devices, and more particularly to ophthalmic lenses for influencing myopia progression in an eye of a subject and methods for designing lenses therefor. Background Art

[0002] Myopia (also known as nearsightedness) is an eye condition in which light rays from distant objects focus in front of the retina, rather than on it. This causes distant objects to appear blurry to the observer, while nearby objects remain clear. Other symptoms can include headaches and eyestrain, while severe myopia increases the risk of retinal detachment, cataracts, and glaucoma. Myopia is the most common eye problem and affects an estimated 1.5 billion people worldwide (22% of the population).

[0003] The adolescent eye typically continues to develop until the age of 18 to 21, with the progression of myopia. By the time the eye is fully developed, it may be severely myopic and difficult to treat. Therefore, according to some estimates, effective preventive measures for myopia and its progression have the potential to improve the vision of 2 billion to 5 billion people worldwide by 2050. Current interventions to prevent the progression of myopia in adolescents include pharmacological agents, frame glasses and contact lenses, each of which presents its own set of challenges. Most current myopia control frame glasses lens designs include a concentric treatment zone. However, concentric treatment zones can cause compliance issues. Contact lenses and pharmacological agents are invasive and require adult assistance, and the use of pharmacological agents may also result in significant side effects.

[0004] Generally speaking, vision involves more than just the eyes. Depending on what we choose to focus on, seeing involves tilting our head and flexing our neck, which affects the position of the entire cervical spine and, therefore, the body's skeletal structure and musculature. For children, whose bones and muscles are still developing, how they habitually position their bodies is particularly important for their future healthy development. This complete relationship between vision and posture, which affects the health of the entire body, should be considered when treating vision, and this is especially true when treating children's vision. Maintaining a child's good, natural posture is essential for managing their vision, ensuring healthy growth, and preventing the potentially harmful future effects of postural disorders.

[0005] Posture is defined as any position the body assumes to maintain balance, maximizing stability, minimizing energy expenditure, and minimizing stress on anatomical structures. Dynamic posture is defined as the way an individual holds their body during movement, while static posture refers to the body's position at rest. The key to good posture is spinal position, which means maintaining, rather than increasing, the three natural curves of the spine: the neck, mid-back, and lower back. Good posture means preventing skeletal misalignment, strain on muscles, joints, and ligaments, and the resulting fatigue and pain.

[0006] Research has highlighted the importance of proper posture, particularly for children, and specifically regarding neck flexion and eye deflection. Studies examining postural behavior during various near vision tasks have shown that children tend to develop various combinations of head and eye deflections during these tasks. Numerous studies have documented evidence of the harmful effects of habitual high neck flexion and repetitive postural habits. Poor postural habits can affect children's attention levels and performance, while also profoundly impacting many aspects of their musculoskeletal system and general health, and can have serious repercussions for future physiological development.

[0007] By misaligning the body's natural structures and placing stress on various body parts, poor posture can be extremely damaging to vital systems and structures, especially when developed early and maintained throughout life. Poor posture can also have additional detrimental effects. In particular, incorrect posture can place an additional strain on the cardiovascular system, negatively impacting the circulatory and nervous systems. Furthermore, it can affect blood pressure, as cervical misalignment can alter it. Specifically, subjects whose posture is characterized by a forward head posture had higher systolic and peripheral arterial blood pressure.

[0008] Poor posture can also affect concentration, performance, and fatigue. Postural changes have been negatively correlated with concentration, while students with correct posture have shown improved performance on mental arithmetic exercises compared to those who sit upright or slouched. Furthermore, some studies have shown that improving posture in students with learning difficulties improves their overall performance. Researchers suggest that maintaining an upright, head-up posture makes it easier to engage in positive and empowering thoughts. This reduces fear of failure and leads to better performance.

[0009] Muscle fatigue, including that associated with misaligned posture, degrades active attention resources, and reducing this muscle strain reduces attention loss. It has also been shown that incorrect posture in children and adolescents can adversely affect their entire metabolism, including cardiopulmonary function and the skeletal system. Schoolchildren are particularly susceptible to neck pain due to prolonged static postures and poor postural habits. Neck pain is a serious health problem for both children and adults. Slouching in a forward-bent posture with the head and trunk leads to increased postural tension and increased compressive forces in the cervical spine, and changes the alignment of the head and trunk relative to the lumbopelvic region. Prolonged forward-bent neck posture puts pressure on the ligaments of the upper cervical spine, leading to fatigue and its subsequent effects.

[0010] In addition to musculoskeletal misalignment, poor posture can lead to spinal erosion, making it fragile and prone to injury; reduced joint mobility; disrupted balance; and an increased risk of falls, often with painful consequences. Studies have shown that poor posture can even negatively impact digestion and respiratory function.

[0011] Given the high usage of smartphones and various screens today, and the increasingly younger age of users, how this behavior affects body posture is particularly relevant, as users often bend over to use their devices. When an individual uses their smartphone (e.g., typing), the lower the head is bent, the more muscle activity is generated (including the erector spinae muscles along the length of the spine), and the gravitational pull of the head increases stress on the neck, spine, and muscles. This posture position results in higher neck discomfort scores compared to those of individuals with a head tilt of 0° (i.e., the head is straight rather than bent downward). Some studies have shown that prolonged neck flexion angles of 15°-20° or less (a more natural position) can prevent neck discomfort. Further research has shown that there are significant differences in muscle activity at different neck flexion angles. It has been shown that continuous forward flexion of the neck leads to increased compressive loads on the cervical spine and a creep response in the surrounding soft tissues. In addition, the root cause of pain is attributed to the excessive loads on the neck and shoulder girdle muscles generated, especially during low-load repetitive tasks, such as prolonged use of handheld devices.

[0012] If viewing position and habitual posture have important consequences, this is especially true for children, whose underdeveloped musculoskeletal systems differ significantly from those of adults (with a larger head-to-body ratio). This puts additional stress on a child's neck muscles, which have to work harder than those of an adult. The relatively higher levels of force on a child's neck structures (including tendons, bones, and joints) can lead to muscle overuse and pain. This has been demonstrated in studies showing increased reports of discomfort when children used screens that required the head to be tilted downward, compared to screens that were positioned higher, allowing the head to be straightened.

[0013] In addition, when the spine is flexed forward, the weight of the head on the spine increases dramatically, and as the head tilts further, the weight increases gradually. In fact, a fully grown head weighs almost 5 kg in a neutral position. The more the head is flexed, the more the force on the neck increases, and at 15 ° it reaches more than twice (about 12 kg). The burden of the head weight increases to 18.14 kg at 30 °, and to 22.23 kg at 45 °, reaching more than 5 times the effect at 60 °, weighing 27.22 kg. In addition to the importance of neck flexion, the frequency of head flexion also increases the load on the physiological functions of the neck. Frequent forward flexion can cause changes in the cervical spine, curvature, supporting ligaments, tendons, muscle tissue and bone segments, which usually cause undesirable posture changes and chronic pain in the neck, upper back and associated subregions.

[0014] Research has further shown that musculoskeletal neck pain, a multifactorial condition, is increasingly common in children and adolescents. Known risk factors for the development of this condition are repetitive motions, such as bending the head, neck, and shoulders to use mobile phones and portable devices, twisting the neck while sitting, studying, or watching television, or repeatedly bending the head and neck backward to look upward. These motions gradually increase stress in the cervical spine, which can lead to various complications, such as premature wear, tear, degeneration, the potential need for surgery, as well as developmental, medical, psychological, and social complications.

[0015] Postural discomfort and its potential harmful effects should be avoided for children, whose posture and musculoskeletal systems are fragile and still developing. To avoid postural discomfort and potential damage, children need comfortable vision wearing glasses that allow easy and natural eye movements during a variety of near and intermediate vision tasks in order to maintain a natural, comfortable and healthy body posture.

[0016] Studies of children's posture during various near vision tasks have shown that their posture, degree of neck flexion, and eye droop vary depending on the type of task. Even the definition of "near work" varies by task, with differences found depending on whether the task is passive, such as reading, or active, such as writing or using a tablet or smartphone. Across various near tasks, natural eye deflection has been found to range, on average, from approximately 15° to 21°. This is important because there is no single viewing pattern for all near vision tasks. Eye direction and body posture naturally vary depending on the nature of the task.

[0017] Another factor to consider regarding children's vision and posture is that children's world is lower than that of adults. That is, children are generally shorter and can easily focus on things at their own height level. When children focus on the "higher" world, taller adults, objects designed for the adult world, or looking up at the sky, they often have to raise their heads or even bend their heads backwards.

[0018] Therefore, there is a need in the art to provide myopia control lenses that are designed to provide optimal vision in a full range of natural postures for all tasks, allowing for a comfortable viewing angle to the top of the lens and keeping head movement as minimal as possible. Summary of the Invention

[0019] The present disclosure is intended to provide a new spectacle lens (e.g., a free-form lens) designed for myopia control (i.e., minimizing and controlling myopia progression). The lenses of the present disclosure can slow myopia progression and axial elongation while providing visual comfort and compliance. In particular, to protect the health and well-being of children, the present disclosure provides a new myopia control lens design characterized by a vertical channel that provides children with a substantially clear visual zone for long-range, intermediate-range, and near-range tasks while maintaining a more comfortable and healthier posture. The unique configuration of the lens provides excellent vision for long-range, intermediate-range, and near-range tasks while ensuring a comfortable and healthy posture for the wearer. The periphery of the lens incorporates a power profile distribution with relatively more positive power than the central aperture, thereby producing peripheral defocus. The unique configuration of the lens allows children to achieve flexible and natural eye deflection for near and intermediate-range tasks, thereby minimizing neck flexion. This innovative lens design maintains children's natural behavior, allowing free movement and comfortable use throughout the day. Therefore, the present disclosure provides an ergonomically designed lens that minimizes and controls myopia progression while also protecting healthy physiological development. In this regard, it should be understood that the visual experience while wearing the glasses is crucial, as the therapeutic effect depends on the wearing time. The inventors have demonstrated that the lenses of the present disclosure achieve similar wearing times compared to a control group throughout all waking hours. To date, this is one of the longest wearing times reported for myopia control frame spectacle lenses in clinical trials (14±1.4 hours a day, including weekends). This is related to the more natural appearance and ergonomic advantages of the lens's vertical channel design, which is designed to enable flexible vertical eye movement to any distance and eliminate the need for head and neck repositioning. This is particularly useful for today's digital lifestyle, as children spend a lot of time focusing on close-up tasks, such as writing, reading, using smartphones, computers, etc. The unique contour distribution of the lenses is intended to minimize stress on children's head, neck, and upper body muscles. During the clinical trial, the overall comfort score reported after one year was 9.07±1.6, compared to 9.38±1.1 in the control group. Despite the presence of peripheral defocus zones in the lenses of the present disclosure, the comfort ratings remained very similar, indicating that children wearing eyeglasses using the lenses of the present disclosure had a positive visual experience.

[0020] When treating a child's vision, not only must the child's eyes be considered, but all of the aforementioned factors must also be considered. Therefore, the optical lens designs of the present disclosure make it possible to improve vision while also considering how body posture is affected. The optical lenses of the present disclosure allow for natural posture during close-range tasks, particularly continuous or repetitive tasks. The optical lenses of the present disclosure allow for the avoidance of the long-term, potentially harmful effects of poor posture on children.

[0021] Because the type of near vision task determines the degree to which a child lowers their eyes and tilts their head, the lens designs of the present disclosure allow the child visual flexibility to achieve natural body movements during near tasks.

[0022] The lenses of the present disclosure allow for flexibility, freedom of movement (particularly needed by children), and natural posture while optimizing vision, visual comfort, and safeguarding the child's development and future well-being.

[0023] Most clinically tested myopia control lenses available today use a concentric design, meaning treatment is applied around the center of the lens. This can cause discomfort with near tasks, leading to unnatural postural adjustments and requiring children to tilt their heads back when looking upwards in order to observe the adult world around them.

[0024] The lens of the present disclosure includes a vertical power profile distribution, which defines a vertical channel, which extends along the vertical meridian of the ophthalmic lens to at least one of the bottom boundary and the top boundary of the ophthalmic lens, and the vertical channel is substantially free of distortion, thereby producing a substantially clear visual zone. The term "border" hereinafter refers to the border of the lens (representing the finished lens installed in the frame of the frame glasses) after the lens is cut according to the frame. This allows the wearer (e.g., a child) to simply guide their natural gaze without having to adjust their head and posture for focusing, thereby enabling near vision focusing in a comfortable and natural posture of the wearer. It should be noted that the lens of the present disclosure can be integrated into frame glasses, or can be configured as a contact lens.

[0025] It should be noted that the vertical channel, which is essentially free of distortion and achieves sharp vision zones for distance, intermediate, and near tasks while maintaining a more comfortable and healthier posture, extends above the optical center to the very edge of the lens. It reaches higher powers only in the area of ​​the upper lens that exits from the frame. The vertical channel's zoning can be considered "defined" by the 0.5 [D] of residual (unwanted) cylindrical profile.

[0026] The vertical channel of the lens defines a unique shape that provides a balance between substantially sharp distance and near vision zones and a through-focus treatment zone for myopia control. Through-focus can be continuous toward the periphery to minimize interference with the visual experience in the vertical plane. Through-focus is applied via an add power with a progressive profile (i.e., the add power is positive power introduced in addition to the power required to correct the refractive error associated with the eye's distance vision). The added power profile introduced along the horizontal meridian (both temporally and nasally) begins at the center of the lens and gradually increases until it reaches approximately 3 [D] at 30-35 degrees without interfering with the wearer's overall comfort when looking through the central zone of the lens. The maximum through-focus added power occurs in the nasal and temporal periphery along the horizontal meridian. However, as this add power increases along the horizontal axis, a smaller degree of continuous add power is also present at the bottom of the channel without clinically significant residual cylinder. This configuration does not hinder the wearer's comfort during both visual and near vision tasks. It strikes the best balance between wearability, introducing a sufficiently clear vision zone, and effective myopia control treatment via the defocused zone.

[0027] The lenses of the present disclosure offer a unique balance between effective myopia control progression and minimal wearer disruption, enabling longer wear times. The gradual increase in add power has a relatively steep gradient, resulting in an asymmetric vertical profile with respect to the horizontal meridian, the bottom region of which may be narrower than the top region. The progressive profile is adapted to mitigate and potentially eliminate hyperopic defocus in the peripheral regions of the retina, preferably by introducing myopic defocus in these peripheral regions. The myopic defocus is intended to influence / control the progression of myopia.

[0028] Additionally, it should be noted that this level of increase in add power allows for a reduction in lens edge thickness, resulting in a more aesthetically pleasing lens. Furthermore, this level of increase in add power reduces the facial distortion ("cut-in effect") produced by negative lenses that appear through the lens. This facial distortion is due to the inward displacement of the face caused by the prismatic effect of the negative lens. It should be noted that the aesthetic properties of the lens enhance both wearer comfort and adaptability, thereby promoting longer wear times.

[0029] As mentioned above, the geometry of the vertical channel makes it possible to eliminate the need for head / neck repositioning, thereby achieving a low to minimal and comfortable and natural neck flexion angle, as well as minimal repetitive head / neck adaptive movements. The lens of the present disclosure is configured to control the progression of myopia in a subject (e.g., a young child) while minimizing stress on the child's head, neck, and upper body muscles. It protects the health of the spine, joints, and ligaments, and this means not only optimized vision, but also improved concentration and performance, while safeguarding the child's development, future health, and well-being.

[0030] The ophthalmic lens of the present disclosure is configured to: (i) correct myopia associated with the fovea region of the wearer's retina, and (ii) achieve myopic defocus in the peripheral region of the wearer's retina to influence the growth process of the wearer's eye, thereby controlling the progression of myopia in the wearer's eye. The ophthalmic lens is configured to be disposed on wearable eyewear.

[0031] The first zone of the vertical channel is positioned at the optical center of the ophthalmic lens. In this regard, it should be noted that in single-vision lenses, the optical center of the lens matches the fitting point. The diopter of the first zone is based on the wearer's myopia. The first zone of the vertical channel is intended to correct vision according to the ophthalmic prescription. In this regard, the wearer's myopia is determined, for example, by conventional myopia measurement techniques, and the diopter of the first zone is determined based on the determined myopia of the wearer's eye. Thus, the first zone of the vertical channel functions to correct myopia associated with the foveal region of the retina. Therefore, the first zone can be described as a zone that supports the primary (foveal) visual acuity according to the wearer's prescription, and it can reasonably be defined as a zone within the outline of 0.5 [D] (diopters) of surface astigmatism (residual cylinder), extending from the optical center along the horizontal meridian to approximately 5 mm. As used herein, the term "approximately" means plus or minus 10%.

[0032] As used throughout this disclosure, the terms "residual cylinder" and "residual cylinder" are used to indicate the cylinder introduced at a point or subarea on the surface of a lens relative to the cylinder that is part of the prescription, if any.

[0033] The lens has through focus areas that extend substantially horizontally from the edge of the vertical channel and gradually increase toward the nasal and temporal regions of the lens, the through focus areas being configured for treating a patient, particularly a child, to reduce myopia progression. The through focus areas have increased power (positive power difference / change) compared to the vision correction prescription. The special lens defines a power profile distribution that is substantially symmetrical about the vertical axis (y-axis) / meridian of the ophthalmic lens, but less symmetrical about the horizontal axis (x-axis) / meridian of the ophthalmic lens. In some possible embodiments, the power profile distribution may be achieved / implemented on the posterior surface of the ophthalmic lens, and the anterior / front surface of the lens may be spherical.

[0034] The method of designing a lens comprises, inter alia, obtaining a prescription (Rx) of a wearer (i.e., a central refractive error of the eye), wherein the prescription comprises on-axis optical parameters including at least one of spherical power, cylindrical power, axial value, or prismatic power. The off-axis maximum add power has a constant value and is not individually designed.

[0035] Specifically, the lens includes a channel-shaped subzone defined by a 0.5 [D] residual cylinder profile, the subzone defining a first optical zone intended to achieve substantially sharp foveal vision, and a second optical zone having a slight add power with a progressive profile. In this regard, it should be noted that the optical power profile of the ophthalmic lens includes at least one through-focus zone that at least partially surrounds the first optical zone and is configured to provide a through-focus add power that extends substantially from the edge of the vertical channel and gradually changes in the temporal and nasal directions, thereby enabling focusing of distance images in front of the nasal peripheral retina and / or on the temporal peripheral retina, respectively, and minimizing peripheral hyperopic defocus. The ophthalmic lens is also configured to achieve myopic defocus in the peripheral region of the wearer's retina to influence eye growth, thereby controlling myopia progression in the wearer's eye. Because the subzone defined by the vertical channel is substantially free of distortion, the second optical zone of the vertical channel is also substantially free of distortion. However, this second optical zone is also part of the through-focus zone. Add power is the positive power introduced beyond that required to correct the eye's refractive error. The added profile along the horizontal meridian (both temporally and nasally) begins at a minimum at the center of the lens and gradually increases in both directions until it reaches approximately 3 [D] of add power at the 30-35 degree zone. The vertical add profile is primarily introduced in the lower zone of the lens and reaches approximately 1 [D] at approximately the -30 degree zone.

[0036] Thus, according to one broad aspect of the present disclosure, an ophthalmic lens for influencing myopia progression in an eye of an individual having a specific prescription (Rx) is provided. The lens has a smooth and clear design without any visible patterns on the lens surface. The lens includes a power profile distribution defining a vertical channel having a bottom apex defining a substantially U-shape, extending along a vertical meridian of the ophthalmic lens to at least one of a bottom boundary and a top boundary of the ophthalmic lens. The vertical channel is substantially free of distortion (e.g., distortion associated with astigmatism). The vertical channel includes a first optical zone disposed about the optical center of the ophthalmic lens and extending to the top boundary of the ophthalmic lens. The first optical zone is configured to provide a first optical power according to a specific prescription (Rx). The vertical channel also includes a second optical zone located at its bottom apex and configured to provide a vertical additional power extending from the first optical zone. The power profile distribution also includes at least one through focus zone that at least partially surrounds the first optical zone and is configured to provide a through focus add power that extends substantially from an edge of the vertical channel and gradually varies in the temporal and nasal directions, thereby enabling focusing of distant images in front of the nasal peripheral retina and / or on the temporal peripheral retina, respectively, and minimizing peripheral hyperopic defocus, such that the ophthalmic lens is configured to: (i) correct myopia associated with the foveal region of the wearer's retina, and (ii) achieve myopic defocus in the peripheral region of the wearer's retina to influence the growth of the wearer's eye, thereby controlling the progression of myopia in the wearer's eye.

[0037] In some embodiments, the through focus add power is distributed symmetrically with respect to a vertical meridian of the ophthalmic lens and asymmetrically with respect to a horizontal meridian of the ophthalmic lens.

[0038] In some embodiments, the vertical channel is symmetrical about the vertical meridian of the ophthalmic lens and asymmetrical about the horizontal meridian of the ophthalmic lens. For example, the vertical channel is symmetrically located about a center point on the horizontal meridian and has a width of 10 mm. The channel is defined by a 0.5 [D] cylindrical line, which means that in the vertical direction, it reaches about 20 degrees (about 10 mm) upward and about 33 degrees (about 16 mm) downward.

[0039] In some embodiments, the first optical zone includes an add power that has a minimum of about 0.01 [D] at a radius of about 1 mm and increases to about 0.1D at a radius of about 2-3 mm and increases to about 0.5D in the horizontal direction from a specific prescription (Rx) within a range of about 5-6 mm from the optical center.

[0040] In some embodiments, the vertical channels are configured to extend horizontally to about 5 mm on each side of the optical center and vertically to about 10 mm above the optical center.

[0041] In some embodiments, the vertical channel includes partitions defined by a profile of about 0.5 [D] residual cylindrical extending horizontally and vertically.

[0042] In some embodiments, the vertical channels extend from the optical center to about 5 mm on each horizontal side.

[0043] In some embodiments, the residual cylinder reaches a value of about 0.5 [D] at about 15-16 mm below the optical center along the vertical meridian.

[0044] In some embodiments, the vertical and through focus add powers are distributed symmetrically with respect to a vertical meridian of the ophthalmic lens and asymmetrically with respect to a horizontal meridian of the ophthalmic lens.

[0045] In some embodiments, the maximum through focus add power has a constant maximum value that is independent of the individual and is independent of the vertical add power.

[0046] In some embodiments, the through focus add power reaches a value of about 0.5 [D] at a radial distance along the horizontal meridian within a range of about 5-6 mm from the optical center.

[0047] In some embodiments, the vertical add power reaches a value of about 0.5 [D] at a radial distance within about 9 mm below the optical center along the vertical meridian.

[0048] In some embodiments, the vertical add power reaches a value in the range of about 0.50-1.00 [D] at a radial distance of about 9-15 mm below the optical center along the vertical meridian.

[0049] In some embodiments, the through focus add power reaches a value of about 2.5 [D] at a radial distance of about 25 degrees from the optical center along the horizontal meridian.

[0050] In some embodiments, the through focus add power reaches a value of about 3 [D] at a radial distance along the horizontal meridian within a range of about 30-35 degrees from the optical center.

[0051] In some embodiments, the power profile is implemented by the back surface of the lens.

[0052] According to another broad aspect of the present disclosure, a method for designing at least one ophthalmic lens for influencing myopia progression is provided, the method comprising: obtaining an ophthalmic prescription for a subject; configuring a vertical channel to be substantially free of distortion, having a bottom apex defining a substantially U-shape and extending along a vertical meridian of at least one ophthalmic lens to at least one of a bottom boundary and a top boundary of the ophthalmic lens; having a first optical zone for providing a first optical power according to a specific prescription (Rx) for a corresponding eye; and a second optical zone for providing a vertical add power. The first optical zone may be disposed about an optical center of the at least one ophthalmic lens and extend to a top boundary of the ophthalmic lens. The second optical zone may be located at the bottom apex of the vertical channel.

[0053] In some embodiments, the method further comprises measuring a specific prescription (Rx) for at least one eye.

[0054] In some embodiments, the method further comprises configuring at least one through-focus zone, the through-focus zone at least partially surrounding the first optical zone, for providing a through-focus add power that extends substantially from an edge of the vertical channel and gradually changes in a temporal and nasal direction along a horizontal meridian to focus a distant image in front of the nasal peripheral retina and / or the temporal retina, respectively, and minimize peripheral hyperopic defocus. The through-focus add power may reach a predefined maximum value at a predefined distance from the edge of the vertical channel of the at least one ophthalmic lens.

[0055] In some embodiments, configuring at least one through-focus zone includes determining a function indicative of a difference between add power along a vertical meridian and a horizontal meridian of the ophthalmic lens.

[0056] In some embodiments, determining the add power further comprises applying a linear fit to a function indicative of a difference between the add power along a vertical meridian and a horizontal meridian of the ophthalmic lens.

[0057] In some embodiments, the method further comprises providing a lens having a vertical channel and a through-focus region.

[0058] According to another broad aspect of the present disclosure, there is provided a processing unit for providing a personalized lens optical property profile distribution, the processing unit comprising: a data input tool configured and operable to receive a specific prescription (Rx) of an individual; a data processing tool configured and operable to determine an additional optical power that gradually varies in the temporal and nasal directions; and a data output tool configured and operable to provide a lens optical property profile distribution, the lens optical property profile distribution defining a vertical channel, the vertical channel being substantially free of distortion, extending from the optical center to at least one of the top and bottom boundaries of the lens, the vertical channel comprising a first optical zone having an optical correction according to the Rx of the eye, a second optical zone for providing a vertical progressive optical power, and a through focus area for providing an additional progressive optical power. BRIEF DESCRIPTION OF THE DRAWINGS

[0059] In order to better understand the subject matter disclosed herein and to illustrate how the same may be carried out in practice, embodiments will now be described, by way of non-limiting example only, with reference to the accompanying drawings, in which:

[0060] Figures 1A to 1C shows a schematic diagram of an ophthalmic lens according to some embodiments of the presently disclosed subject matter, a possible optical power addition diagram, and a possible cylindrical power distribution diagram, respectively;

[0061] Figure 2A and Figure 2B Shown respectively Figures 1A to 1C a graph of an add power profile distribution of an ophthalmic lens as a function of distance from the optical center and an associated add power gradient graph;

[0062] Figure 3A and Figure 3B Shown respectively Figures 1A to 1C A graph of the residual cylinder profile distribution of an ophthalmic lens as a function of distance from the optical center and the associated residual cylinder gradient graph.

[0063] Figure 4A and Figure 4B shows possible power addition and residual cylinder diagrams, respectively, for ophthalmic lenses according to some possible embodiments of the present disclosure;

[0064] Figure 5A and Figure 5B Shown respectively Figure 4A and Figure 4B a graph of an add power profile distribution of an ophthalmic lens as a function of distance from the optical center and an associated add power gradient graph;

[0065] Figure 6A and Figure 6B Shown respectively Figure 4A and Figure 4B A graph of residual cylinder profile distribution of an ophthalmic lens as a function of distance from the optical center and an associated residual cylinder gradient graph;

[0066] Figure 7A and Figure 7B A comparison of some optical properties of lenses of the present disclosure having different maximum add powers is shown, wherein Figure 7A shows a comparison of the difference in add power along the horizontal meridian and the vertical meridian, and Figure 7B A comparison of the residual cylindrical power difference along the horizontal meridian and the vertical meridian is shown;

[0067] Figure 8A and Figure 8B Shown Figure 7A and Figure 7B Comparison of the gradient profile distribution difference of the lens along the horizontal meridian and the vertical meridian, where Figure 8A shows a comparison of the add power gradient differences, and Figure 8B A comparison of the residual cylindrical power gradient differences is shown;

[0068] Figure 9 A functional flow chart illustrating a method for designing at least one ophthalmic lens according to some possible embodiments of the present disclosure is shown;

[0069] Figure 10A and Figure 10B Shown Figure 7A and Figure 7B Linear fit of the curve depicted in ;

[0070] Figure 11 A functional block diagram of a processing unit for providing a personalized lens optical property profile distribution according to some possible embodiments of the present disclosure is shown. DETAILED DESCRIPTION

[0071] One or more specific and / or alternative embodiments of the present disclosure will be described below with reference to the accompanying drawings, and these embodiments should be considered to be merely illustrative in all respects and not to be limiting in any way. It should be apparent to those skilled in the art that these embodiments may be practiced without such specific details. In order to provide a concise description of these embodiments, all features or details of the actual implementation are not described in detail in the specification. It is not important that the elements shown in the drawings are not necessarily to scale or that the proportional relationships are incorrect. Instead, the focus is on clearly illustrating the principles of the present disclosure so that once those skilled in the art understand the principles of the subject matter disclosed herein, they will be able to make and use its enhanced terrestrial communications. Without departing from the essential characteristics described herein, the present disclosure may be provided in other specific forms and embodiments.

[0072] Any reference in the specification to a method shall apply, mutatis mutandis, to an apparatus or system capable of executing the method and / or to a non-transitory computer-readable medium storing instructions for executing the method. Any reference in the specification to a system or apparatus shall apply, mutatis mutandis, to a method executable by the system and / or to a non-transitory computer-readable medium storing instructions executable by the system. Any combination of any modules or units listed in any figure, any part of the specification, and / or any claim may be provided.

[0073] refer to Figures 1A to 1C , which respectively show schematic diagrams of ophthalmic lenses 10 according to some embodiments of the presently disclosed subject matter ( Figure 1A ), possible additional power distribution diagram ( Figure 1B ) and possible cylindrical power distribution diagram ( Figure 1C ). Figure 1A A lens 10 is shown that is intended to influence and control myopia progression in the eye of an individual (e.g., a child) having a specific prescription (Rx). Typically, the prescription (Rx) includes optical parameters that include at least one of spherical power, cylindrical power, axial value, add power, or prismatic power. The ophthalmic lens 10 can be integrated into eyeglasses or contact lenses. The ophthalmic lens 10 defines a vertical meridian VM and a horizontal meridian HM that intersect at the optical center OC of the ophthalmic lens 10.

[0074] As shown, the lens 10 defines a power profile that defines a vertical channel 12 configured to be substantially free of distortion, having a bottom apex defining a substantially U-shape and extending along a vertical meridian VM of the ophthalmic lens 10 to at least one of a bottom boundary 10b and a top boundary 10t of the ophthalmic lens. Figures 1A to 1CIn a non-limiting example, the vertical channel 12 extends vertically through 30 degrees (15-16 mm) to the bottom boundary 10b of the ophthalmic lens 10, through about 20 degrees (9-10 mm) to the top boundary 10t of the lens, and horizontally through about 10 degrees (5-6 mm) from the optical center OC to the nasal side and from the optical center OC to the temporal side, thereby defining a width of about 10 mm. The vertical channel 12 is configured to be substantially free of distortion, i.e., below clinically significant residual (unwanted) cylindrical power. Generally speaking, the vertical channel 12 may have residual cylindrical power at its periphery, but this residual cylindrical power is below the astigmatism sensitivity threshold of the eye (about 0.5D) and therefore does not inconvenience the user. In this way, the vertical channel 12 is configured to enable an individual (e.g., a child) to assume his / her natural posture, i.e., minimizing the need to reposition the head, neck, or upper body muscles. As Figure 1C As best seen in FIG. 1 , the vertical channels 12 may have partitions defined by residual lenticular profiles / contours of 0.5 [D].

[0075] The vertical channel 12 defines a first optical zone 12A, which is defined by a 0.5 [D] residual cylindrical profile, as described above. Figure 1A and Figure 1B As best seen in FIG, the vertical channel 12 may have a first optical zone defined by a residual cylindrical profile / contour of 0.5 [D]. Figure 1A and Figure 1BAs best shown in FIG. 1 , the vertical channel 12 includes a first optical zone 12A disposed about the optical center OC and extending from the optical center OC through approximately 20 degrees (approximately 9-10 mm) to a top boundary 10t and to approximately 18-20 degrees (approximately 9-10 mm) below the optical center OC. The first optical zone 12A is configured to provide optical power according to the wearer's prescription (Rx), thereby supporting the wearer's central vision. The vertical channel 12 also defines a second optical zone 12B that extends from the first optical zone 12A and provides a gradually increasing vertical add power. More specifically, the second optical zone 12B includes a slight increase in optical power (0.5D-1.00D) at approximately -20 to -30 degrees (9 mm-15 mm) below the optical center OC. Optionally, and in some embodiments, preferably, the vertical channel 12 is substantially symmetrical about the vertical meridian VM of the ophthalmic lens and asymmetrical or asymmetric about the horizontal meridian HM of the ophthalmic lens. For example, the relative add power increases gradually in the horizontal direction until it reaches 3.00 [D] at about 16 mm from the optical center of the lens, and in the vertical direction, the relative add power reaches 1.00 [D] at about 15 mm below the optical center of the lens along the vertical meridian. Depending on the frame size, the relative add power at the lower edge ranges from 1.00 to 1.50 D.

[0076] The optical power profile of the lens 10 further defines a through-focus zone 14 at least partially surrounding the first optical zone 12A. The through-focus zone 14 extends to the border / edge of the ophthalmic lens 10, thereby defining a nasal peripheral zone 14n and a temporal peripheral zone 14t. The through-focus zone 14 is configured to provide a through-focus add power P relative to the prescribed power. The through-focus add power P may gradually increase in the temporal and nasal directions, toward the border of the ophthalmic lens 10, thereby enabling distant images / objects to be focused in front of the nasal peripheral retina and / or the temporal retina, respectively, and minimizing peripheral hyperopic defocus.

[0077] exist Figure 1B In a non-limiting example, the through focus add power P of the through focus zone 14 at the nasal and temporal peripheries reaches a maximum value of about 3.00 [D] relative to the prescription power. However, the lens 10 can generally be designed to have a higher or lower maximum through focus add power P. The purpose of the through focus zone 14 of the ophthalmic lens 10 is to affect myopic defocus in the peripheral region of the retina. The through focus add power P of the through focus zone 14 is intended to eliminate as much of the peripheral hyperopic defocus as possible, preferably by introducing myopic defocus. The purpose of affecting myopic defocus in the peripheral region of the retina is to influence / control the development of myopia and thereby control the progression of myopia in the eye. Therefore, the through focus zone 14 is not intended to correct myopia or hyperopia associated with the peripheral region of the retina.

[0078] This particular configuration of the ophthalmic lens 10 enables: (i) correcting myopia associated with the foveal region of the subject / wearer's retina, and (ii) achieving myopic defocus in the peripheral region of the wearer's retina to influence the growth of the wearer's eye, and thereby influence the progression of myopia in the wearer's eye.

[0079] The first optical zone 12A may have a zone (width) of approximately 10-12 mm, i.e., it extends horizontally (along the horizontal meridian HM) 5 mm-6 mm in the nasal and temporal directions from the optical center OC. In some embodiments, the first optical zone 12A adopts the wearer's prescription (Rx) at approximately the optical center of the lens, with a minimum add power of 0.01 [D] at a radius of 1 mm, and increases from the prescription power to approximately 0.1 D at approximately 2-3 mm from the optical center OC, and increases to an add power of approximately 0.5 D at approximately 5-6 mm temporally and nasally from the optical center OC along the horizontal meridian HM. In the second optical zone 12B, the vertical add power may reach a value of approximately 0.5 [D] at a radial distance within the range of approximately 9 mm-10 mm below the optical center OC along the vertical meridian VM, and reach a value of approximately 1.00 [D] at a radial distance of approximately 30 degrees (approximately 15 mm) below the optical center OC along the vertical meridian VM.

[0080] In some embodiments, the through-focus additional optical power P reaches a value of about 2.5 [D] at a radial distance in the range of about 25-26 degrees (about 12 mm-13 mm) temporally and nasally from the optical center along the horizontal meridian HM, and reaches a value of about 3 [D] at a radial distance in the range of about 30-32 degrees (about 15 mm-16 mm) from the optical center along the horizontal meridian HM.

[0081] Figure 1B and Figure 1C The variation of the add power and residual cylinder over the wearer's field of view (FOV) (within the eyeglass frame) is plotted separately. Thus, the plot is divided by horizontal and vertical lines that represent the angle / eye rotation (in degrees) relative to the center of the FOV, which generally coincides / aligns substantially with the optical center of the lens. The various contour lines / contours correspond to different add powers ( Figure 1B ) and different residual cylindrical powers ( Figure 1C ).exist Figure 1C In the example, the vertical channel 12 is located within the innermost contour corresponding to a residual cylinder of approximately 0.5 D. The residual cylinder gradually increases to approximately 4 D toward the nasal and temporal sides. Figure 1BIn the middle, the add power is about 0.5D (innermost contour) and gradually increases to about 3D at the nasal and temporal peripheries of the lens 10. As shown, the first optical zone 12A almost reaches the upper boundary of the lens. Figure 1B This configuration achieves substantially clear vision for distance, intermediate, and near vision tasks. The primary through-focus areas for an add power of 3 [D] are on the nasal and temporal sides along the horizontal axis.

[0082] refer to Figure 2A and Figure 2B , which graphically show Figures 1A to 1C The ophthalmic lens 10 is as far as the optical center ( Figures 1A to 1C Add power P[D] (vertical and horizontal profiles) as a function of the (radial) distance r[degrees] of the optical axis (OC) and the associated add power slope (gradient)

[0083] In particular, Figure 2A It shows that P(r x ) is a graph of the horizontal meridian ( Figures 1A to 1C The distance r from the optical center OC in the nasal and temporal directions on / along the horizontal meridian x The additional optical power P profile distribution as a function of is represented by curve 21. Figure 2A It is also shown that P(r y ) graph, which is used as Figures 1A to 1C The distance r from the optical center OC on / along the vertical meridian VM y The additional optical power P profile distribution as a function of is represented by curve 22.

[0084] Figure 2B Shown It is P(r x ), represented by curve 23; and It is P(r y ) is represented by curve 24.

[0085] Function P(r x )(Right now, Figure 2A The curve 21 shown is symmetrical about r = 0, and the function P(r y )(Right now, Figure 2B The curve 22 shown is asymmetric about r = 0. In other words, the additional power P can be adjusted relative to the ophthalmic lens ( Figures 1A to 1C 10) are symmetrically distributed about the vertical meridian VM and asymmetrically distributed with respect to the horizontal meridian HM of the ophthalmic lens.

[0086] refer to Figure 3A and Figure 3B , which graphically show C(r), which is Figures 1A to 1C Residual (unwanted) cylinder power C [D] profile distribution of the ophthalmic lens 10 as a function of the distance r [degrees] from the optical center OC; and the associated slope (gradient) More specifically, Figure 3A Shows C(r x ), which is the distance r from the optical center OC in the nasal and temporal directions along the horizontal meridian HM / on said horizontal meridian x The residual cylindrical power C profile distribution as a function of is represented by curve 31. Figure 3A Also shown is C(r y ), which is the distance r from the optical center OC along the vertical meridian VM / on said vertical meridian y The residual cylindrical power C profile distribution as a function of is represented by curve 32.

[0087] Figure 3B Shown It is C(r x ), which is represented by curve 33; and It is C(r y ), which is represented by curve 34.

[0088] like Figure 3A As can be seen in the figure, in the horizontal direction (towards the nasal side and the temporal side), due to the varying add power along the horizontal meridian HM, the residual cylindrical power C profile is symmetrically distributed with respect to the vertical meridian VM of the ophthalmic lens 10, and asymmetrically distributed with respect to the horizontal meridian HM. The residual cylindrical power is approximately and (about 10-12 mm) and in the vertical direction (curve 32) between about and (about 27 mm) remains below 0.5[D], which corresponds to the vertical channel ( Figure 1B and Figure 1C 12) in the partition, the partition is essentially free of distortion, because the residual cylindrical power below 0.5 [D] is not considered clinically significant to the human eye. Therefore, the vertical channel is considered free of distortion.

[0089] refer to Figure 4A and Figure 4B , which respectively show power add profiles of an ophthalmic lens 40 according to some possible embodiments of the presently disclosed subject matter ( Figure 4A ) and residual cylindrical power distribution diagram ( Figure 4B ). The ophthalmic lens 40 has Figures 1A to 1C The same design concept of the ophthalmic lens 10 is used, however, in the ophthalmic lens 40, the maximum add power reaches 4.00 [D] at the nasal and temporal periphery at a distance of about 15 mm from the optical center OC along the horizontal meridian HM. The higher add power of 4.00 [D] may introduce increased myopic defocus in the peripheral area of ​​the retina of the eye.

[0090] refer to Figure 5A and Figure 5B , which graphically show P(r), which is Figure 4A and Figure 4B The profile of the add power P[D] of the ophthalmic lens 40 as a function of the distance r[degrees] from the optical center OC; and the associated slope In particular, Figure 5A is P(r x ) as the distance r from the optical center OC in the nasal and temporal directions along the horizontal meridian HM x The additional optical power additional P profile distribution as a function of is represented by curve 51. Figure 5A Also shown is P(r y ) as a function of the distance r from the optical center OC on / along the vertical meridian VM y The additional optical power additional P profile distribution as a function of is represented by curve 52.

[0091] Figure 5B Shown The graph of P(r x ), which is represented by curve 53; and The graph of P(r y ), which is represented by curve 54.

[0092] Function P(r x )(Right now, Figure 5A The curve 51 shown is symmetric about r=0 and steps up to about 4D in the nasal and temporal peripheries of the lens 40. The function P(r y )(Right now, Figure 5B The curve 52 shown is asymmetric about r=0. In other words, the additional power P can be adjusted relative to the ophthalmic lens ( Figure 4A and Figure 4B 40) are symmetrically distributed about the vertical meridian VM of the ophthalmic lens, and asymmetrically distributed with respect to the horizontal meridian HM of the ophthalmic lens.

[0093] refer to Figure 6A and Figure 6B , which graphically show C(r), which is Figure 4A and Figure 4B The ophthalmic lens 40 is as far as the optical center ( Figures 4A to 4B The residual (unwanted) cylindrical power C[D] profile distribution as a function of the distance r[degrees] of the OC) in FIG; and the associated slope More specifically, Figure 6A Shows C(r x ) as the distance r from the optical center OC in the nasal and temporal directions along the horizontal meridian HM / on said horizontal meridian x The residual cylindrical power C profile distribution as a function of is represented by curve 61. Figure 6A Also shown is C(r y ) as a function of the distance r from the optical center OC along the vertical meridian VM / on said vertical meridian y The residual cylindrical power C profile distribution as a function of is represented by curve 62.

[0094] Figure 6B Shown The graph of C(r x ), which is represented by curve 63; and It is C(r y ), which is represented by curve 64.

[0095] like Figure 6A As can be seen in FIG, in the nasal and temporal horizontal directions, due to the varying add power along the horizontal meridian HM, the residual cylinder C is distributed symmetrically with respect to the vertical meridian VM of the ophthalmic lens 40, and is distributed asymmetrically with respect to the horizontal meridian HM of the ophthalmic lens along the vertical meridian VM. The residual cylinder C in the horizontal direction (curve 31) is and (about 10-11 mm) and in the vertical direction (curve 32) between about and (about 19-20 mm) remains below 0.5 [D], which corresponds to the vertical channel ( Figure 4B 12) in the partition, which is essentially free of distortion, because residual cylinder below 0.5 [D] is not considered clinically significant to the human eye.

[0096] refer to Figure 7A and Figure 7B , which graphically illustrate a comparison of some optical properties of lenses of the present disclosure having different maximum optical add powers. In particular, Figure 7A Three graphs are shown of the difference in add power ΔP(r) between the horizontal meridian and the vertical meridian associated with each of these lenses. The difference in add power ΔP(r) is expressed as:

[0097] ΔP(r)=P(r x )-P(r y )

[0098] Where P(r x ) is the additional power along the horizontal meridian HM, and P(r y ) is the add power along the vertical meridian VM. More specifically, curves 71, 72, and 73 represent ΔP(r)2, ΔP(r)3, and ΔP(r)4 for lenses with maximum add powers of +2.00 [D], +3.00 [D], and +4.00 [D], respectively.

[0099] Figure 7B Three graphs are shown showing the residual cylindrical power difference ΔC(r) between the horizontal meridian and the vertical meridian. The cylindrical power difference ΔC(r) is expressed as:

[0100] ΔC(r)=C(r x )-C(r y )

[0101] Therefore, C(r x ) is the residual cylindrical power along the horizontal meridian HM, and C(r y ) is the residual cylinder along the vertical meridian VM. More specifically, curves 74, 75, and 76 represent ΔC(r)2, ΔC(r)3, and ΔC(r)4 for lenses with maximum add powers of +2.00 [D], +3.00 [D], and +4.00 [D], respectively.

[0102] like Figure 7A and Figure 7B As can be seen from the figure, a larger maximum add power will produce a steeper rise in the add power difference ΔP(r) between the horizontal meridian and the vertical meridian ( Figure 7A ). Therefore, since the residual cylinder is associated with a gradual increase in add power, a larger maximum add power results in a larger maximum cylinder. The increase in maximum cylinder produces a larger difference ΔC(r) between the horizontal meridian and the vertical meridian ( Figure 7B ).

[0103] refer to Figure 8A and Figure 8B , which graphically show Figure 7A and Figure 7B Comparison of the slope difference of the two lenses. In particular, Figure 8A The difference in add power slope between the horizontal meridian and the vertical meridian associated with each of these lenses is shown. Two curves of . Slope difference Expressed as:

[0104]

[0105] thus and They are the additional focal function P(r x ) and P(r y ). In particular, curves 81 and 82 represent the slope differences for lenses with maximum add power of +3.00 [D] and +4.00 [D], respectively. and

[0106] Figure 8B The residual cylinder slope difference between the horizontal meridian and the vertical meridian associated with each of these lenses is shown. Slope difference Expressed as:

[0107]

[0108] thus and They are the residual cylindrical function C(r x ) and C(r y In particular, curves 83 and 84 represent the slope differences of the aforementioned lenses with maximum add power of +3.00 [D] and +4.00 [D], respectively. and

[0109] As can be seen from the figure, a larger maximum add power will produce a difference in the slope of the add power between the horizontal meridian and the vertical meridian. A more obvious rise ( Figure 8A ), and therefore also produces a more obvious residual cylindrical lens slope difference between the horizontal meridian and the vertical meridian ( Figure 8B ).

[0110] refer to Figure 9, which illustrates a functional flow chart of a method 100 for designing at least one ophthalmic lens for influencing myopia progression in an individual's eye. The method 100 may include the following optional steps: obtaining an ophthalmic prescription (Rx) for a subject / individual at 101. The method 100 includes configuring a vertical channel to be substantially free of distortion at 102. The vertical channel may have a bottom apex defining a substantially U-shape and may extend along a vertical meridian of the ophthalmic lens to at least one of a bottom boundary and a top boundary of the ophthalmic lens; configuring a first optical zone at 103 to provide vertical optical power according to a specific prescription (Rx) for a corresponding eye. The first optical zone may be disposed about an optical center of the at least one ophthalmic lens and may extend to a top boundary of the ophthalmic lens; and configuring a second optical zone at 104 to provide vertical add power. The second optical zone may be located at the bottom apex of the vertical channel below the first optical zone.

[0111] In some embodiments, method 100 may further include configuring at least one through-focus zone at least partially surrounding the first optical zone to provide progressive add power at 105. The at least one through-focus zone may extend substantially from an edge of the vertical channel and gradually change in the temporal and nasal directions to focus the distance image in front of the nasal peripheral retina and / or the temporal retina, respectively, and minimize peripheral hyperopic defocus. The progressive add power may reach a predefined maximum value at a predefined distance from the optical center of the at least one ophthalmic lens.

[0112] In some embodiments, configuring at least one through-focus zone in 105 includes determining a function indicative of a difference between the add power along the vertical meridian and the horizontal meridian of the ophthalmic lens in 106. This may be accomplished by applying a linear fit to the function indicative of a difference between the add power along the vertical meridian and the horizontal meridian of the ophthalmic lens in 107. For example, a linear thread may be calculated that indicates a relationship (difference) between the horizontal power profile distribution and the vertical power profile distribution (i.e., the add power along the vertical meridian and the horizontal meridian). The linear thread may be utilized to design an ophthalmic lens according to the subject's prescription.

[0113] In this regard, reference Figure 10A and Figure 10B , which graphically show Figure 7A and Figure 7B In particular, Figure 10AIn the example, linear lines 91a-91c correspond to the general equation y=a1x+b1, whereby a1 may be in the range of -0.05 to -0.13, and b1 may be in the range of -1.11 to -0.39 (linear lines 91a-91c). Linear trends 92a-92c correspond to the general equation y=a2x+b2, whereby a2 may be in the range of 0.08 to 0.16, and b2 may be in the range of -0.67 to -1.43. Figure 10B , linear trends 93a-93c correspond to the general equation y = a3x + b3, whereby a3 may be in the range of -0.25 to -0.13, and b3 may be in the range of -2.47 to -1.2. Linear trends 94a-94c correspond to the general equation y = a4x + b4, whereby a4 may be in the range of 0.08 to 0.19, and b4 may be in the range of -1.75 to -0.8. It should be noted that the general equations y = a1x + b1 and y = a2x + b2 may also correspond to linear trends for various lenses with maximum add powers between 2D and 4D, while the general equations y = a3x + b3 and y = a4x + b4 may correspond to the residual cylindrical power differences associated with these lenses.

[0114] These linear trends can be used to determine the optical profile distribution. For example, for a subject with a prescription of -4.00 [D]sph, using Figure 10A and Figure 10B The corresponding linear lines shown determine the optical power profile distribution, where the first optical zone includes a prescription of -4.00 [D]sph and the through focus areas provide the following add power according to the linear trends defined above: gradually varying up to 0.5 in the temporal and nasal directions up to approximately 12 degrees, gradually varying from 0.5 to 1.5 in the temporal and nasal directions from 10 degrees to 20 degrees, and gradually varying from 1.5 to 3 in the temporal and nasal directions from 20 degrees to 30 degrees.

[0115] refer to Figure 11, which shows a functional block diagram of a processing unit 200 for providing a personalized lens optical property profile. Generally speaking, the processing unit 200 can be a processor, a controller, a microcontroller, or any type of integrated circuit. The control unit 200 is typically configured as a computing / electronic utility, including, among other things, tools such as a data input tool 200A, a data analyzer 200D, and a data output tool 200B. It may also include or be associated with a memory 200C (i.e., a non-volatile computer-readable medium) for storing input / output data, a database, or a computer program. The processor unit can be a processing circuit system. The processing circuit system can be implemented as a central processing unit (CPU) and / or a graphics processing unit (GPU), and / or one or more other integrated circuits, such as an application-specific integrated circuit (ASIC), a field-programmable gate array (FPGA), a full-custom integrated circuit, or a combination of these integrated circuits. A computerized system may include one or more processors and may also include additional units or components, such as a storage unit, a communication unit, etc. The database can be a cloud-based system. In an example, a cloud-based system can be a distributed blockchain system in which multiple parties (e.g., manufacturers, recyclers, retailers) can access a distributed ledger. The latter is a type of internet-based computing that provides shared computer processing resources and data (such as servers, storage, and applications) to computers and other devices through a computer network (or communication network) such as the internet. Cloud computing and storage solutions provide users and businesses with various capabilities to store and process their data in privately owned data centers or third-party data centers, which may be located far away from the users, ranging in distance from across the city to across the world. Therefore, the present disclosure provides for: using cloud computing technology, according to which a central data analyzer (software) is used to receive sensory data from multiple product storage locations; and using these multiple data sources to optimize the identification of product types and product status monitoring mentioned above (e.g., using self-learning patterns, model optimization, etc.).

[0116] Memory 200C may be integrated within processing unit 200 or may be an external storage device accessible by processing unit 200. The software may be downloaded to the processing unit in electronic form, for example, over a network, or alternatively provided on tangible media, such as optical, magnetic, or electronic storage media. The computer program described above, including instructions for implementing the methods described below, may be intended to be stored in memory 200C or on a removable storage medium suitable for cooperating with a reader of processing unit 200. More specifically, the computer program may communicate with an interface to receive order and time data.

[0117] Unless otherwise specifically stated, as will be apparent from the following discussion, it should be understood that throughout the specification, terms such as "determine," "process," and the like are used to refer to computer actions and / or processes that manipulate data and / or transform data into other data. In addition, operations according to the teachings herein may be performed by a computer specially constructed for the desired purpose or by a general-purpose computer specially configured for the desired purpose via a computer program stored in a computer-readable storage medium.

[0118] The data input tool 200A is configured and operable to receive a specific prescription (Rx) (handedness) of an individual. The data input tool 400A may include a communication interface that is appropriately configured to connect the data analyzer 200D to a measurement module that supplies the parameters mentioned above or an external memory (database) that has previously stored such data via wired or wireless signal transmission (e.g., via a communication network). The communication interface may be a separate tool from the processing unit 200, or may be integrated within the processing unit. When the communication interface is a unit separate from the processing unit 200, the processing unit 200 may include a transceiver that allows the processing unit to connect to the communication interface and send and / or receive data. When the communication interface is integrated within the processing unit 200, the communication interface may be included in the data input tool 200A and the data output tool 200B of the processing unit 200.

[0119] The data analyzer 200D is configured and operable to determine an add power that gradually varies in the temporal and nasal directions. The data analyzer 200D may also be adapted to: (i) configure the vertical channel to be substantially free of distortion and include a power according to an Rx prescription; and (ii) configure a through-focus zone having a progressive add power.

[0120] The data output tool 200B is configured and operable to provide a lens optical property profile distribution, the optical property profile distribution defining (i) a vertical channel, the vertical channel being substantially free of distortion, extending from the optical center of the lens to at least one of the bottom boundary and the top boundary of the lens, and comprising a first optical zone having an optical correction according to the Rx of the eye and a second optical zone for providing vertical additional optical power and a through focus zone for providing additional progressive optical power.

[0121] Thus, the functionality of the processing unit 200 may be implemented through suitable circuitry and / or software and / or hardware components including computer-readable code configured to receive the calculated optical design profile distribution indicative of the correction for a specific patient, the optical properties of the through-focus region, and to process the data to generate data representing a physical representation of the optical property profile distribution. Features of the present disclosure may include a general-purpose or special-purpose computer system comprising various computer hardware components. Features within the scope of the present disclosure also include computer-readable media or data structures stored thereon for implementing or having computer-executable or computer-readable instructions. Such computer-readable media may be any available medium that can be accessed by a general-purpose or special-purpose computer system. In this specification and the appended claims, a "processing unit" is defined as one or more software modules, one or more hardware modules, or a combination thereof, that work together to perform operations on electronic data. The physical layout of the modules is not relevant. The processing unit 200 may be configured as an electronic module for collecting and processing data and, optionally, sending instructions to a system capable of creating an optical property profile distribution. In some embodiments, the processing unit 200 is configured and operable to calculate an optical design profile distribution indicative of the correction for a specific patient.

[0122] The term "processing unit" should be broadly interpreted to cover any type of electronic device with data processing capabilities, including, by way of non-limiting example, personal computers, servers, computing systems, communication devices, processors (e.g., digital signal processors (DSPs), microcontrollers, field programmable gate arrays (FPGAs), application-specific integrated circuits (ASICs), etc.), and other electronic computing devices. The control unit may include a general-purpose computer processor that is programmed in software to implement the functions described herein below. In addition, operations according to the teachings herein may be performed by a computer specifically constructed for the desired purpose, or by a general-purpose computer specifically configured for the desired purpose via a computer program stored in a computer-readable storage medium. The different elements of the processing unit (electronic unit and / or mechanical unit) may be interconnected by wires or wirelessly. The software may be downloaded electronically to the processing tool, for example, over a network, or alternatively, the software may be provided on tangible media, such as optical, magnetic, or electronic storage media. Alternatively or additionally, some or all of the functions of the processing unit may be implemented in dedicated hardware, such as a custom or semi-custom integrated circuit or a programmable digital signal processor (DSP).

[0123] The terms "control unit" and "processor means" are used interchangeably herein and refer to a computer system, state machine, processor, etc. that is designed to perform arithmetic or logical operations using a system of logic circuits that respond to and process instructions that drive the computer. The techniques and systems of the presently disclosed subject matter can be applied to various computing or processing environments, such as computer or process-based environments. The techniques can be implemented in a combination of software and hardware. As also described above, the techniques can be implemented in a program executed on a programmable machine (such as a fixed computer configured to obtain raw log data). Program code is applied to data entered using an input device to perform the described techniques and generate output information. The output information can then be applied to one or more output devices. Each program can be implemented in a high-level procedural or object-oriented programming language to communicate with a process-based system. However, if desired, these programs can be implemented in assembly language or machine language.

[0124] In other embodiments, the technology of the presently disclosed subject matter can be utilized in a network computing system and / or environment. Several computer systems can be coupled together via a network (such as a local area network (LAN), a wide area network (WAN), or the Internet). Therefore, each method or technology of the presently disclosed subject matter as a whole or its functional steps can be implemented by a remote network computer or a combination of several remote network computers. Therefore, any functional part of the processing unit 200 can be provided or connected via a computer network. In addition, the control unit can also provide processor services remotely via the network. Each such program can be stored on a storage medium or device, such as a compact disc read-only memory (CD-ROM), a hard disk, a floppy disk, or similar media or device, and when a computer reads the storage medium or device to perform the process described in this document, the storage medium or device can be read by a general or special programmable machine for configuring and operating the machine. The system can also be implemented as a machine-readable storage medium configured with a program, wherein the storage medium configured in this way enables the machine to operate in a specific and predefined manner.

[0125] Relative terms regarding the orientation of the described elements / components, such as "lower," "upper," "horizontal," "vertical," "above," "beneath," "upward," "downward," "top," and "bottom," and their derivatives (e.g., "horizontally," "downwardly," "upwardly," etc.), and similar adjectives, refer to the way the illustration is positioned on the paper and do not limit any orientation in which these elements / components may be used in actual applications.

[0126] It should also be understood that throughout this disclosure, when a process or method is shown or described, the steps / actions of the method can be performed in any order and / or performed simultaneously, and / or with other steps / actions not shown / described herein, unless it is clear from the context that one step depends on another step being performed first. In possible embodiments, not all shown / described steps / actions are required to implement the method.

Claims

1. An ophthalmic lens for influencing myopia progression in an eye of an individual having a specific prescription (Rx), the lens comprising a power profile distribution defining: (i) a vertical channel having a bottom apex defining a substantially U-shape, extending along a vertical meridian of the ophthalmic lens to at least one of a bottom boundary and a top boundary of the ophthalmic lens, the vertical channel being substantially free of distortion; wherein the vertical channel comprises: a first optical zone disposed around the optical center of the ophthalmic lens and extending to the top boundary of the ophthalmic lens, the first optical zone being configured to provide a first optical power according to the specific prescription (Rx); and a second optical zone located at the bottom top of the vertical channel; (ii) at least one through-focus region at least partially surrounding the first optical zone of the vertical channel and configured to provide a through-focus add power that extends substantially from an edge of the vertical channel and gradually varies in a temporal and nasal direction, thereby enabling focusing of a distant image in front of a nasal peripheral retina and / or on a temporal peripheral retina, respectively, and minimizing peripheral hyperopic defocus; wherein the at least one through-focus region includes the second optical zone of the vertical channel; The ophthalmic lens is configured to: correct myopia associated with the fovea region of the wearer's retina; and achieve myopic defocus in the peripheral region of the wearer's retina to affect the growth of the wearer's eye, thereby controlling the progression of myopia in the wearer's eye.

2. The ophthalmic lens of claim 1, wherein the through focus add power is distributed symmetrically with respect to a vertical meridian of the ophthalmic lens and asymmetrically with respect to a horizontal meridian of the ophthalmic lens.

3. The ophthalmic lens of claim 1 or 2, wherein the vertical channel is symmetrical with respect to the vertical meridian of the ophthalmic lens and asymmetrical with respect to the horizontal meridian of the ophthalmic lens.

4. An ophthalmic lens as described in any one of claims 1 to 3, wherein the first optical zone includes an additional optical power that has a minimum value of approximately 0.01 [D] at a radius of approximately 1 mm and increases to approximately 0.1 D at a radius of approximately 2-3 mm and increases to approximately 0.5 D in a horizontal direction within a range of approximately 5-6 mm from the optical center from the specific prescription (Rx).

5. The ophthalmic lens of any one of claims 1 to 4, wherein the vertical channel is configured to extend horizontally to about 5 mm from each side of the optical center and vertically to about 10 mm above the optical center.

6. The ophthalmic lens of any one of claims 1 to 5, wherein the vertical channel comprises a partition defined by a profile extending horizontally and vertically of about 0.5 [D] residual cylinder.

7. The ophthalmic lens of claim 6, wherein the residual cylinder reaches a value of about 0.5 [D] at about 15-16 mm below the optical center along the vertical meridian.

8. The ophthalmic lens of any one of claims 1 to 7, wherein vertical and through focus add powers are distributed symmetrically with respect to the vertical meridian of the ophthalmic lens and asymmetrically with respect to the horizontal meridian of the ophthalmic lens.

9. The ophthalmic lens of claim 8, wherein the maximum through focus add power has a constant maximum value that is independent of the individual and is independent of the vertical add power.

10. The ophthalmic lens of any one of claims 1 to 9, wherein the through-focus add power reaches a value of about 0.5 [D] at a radial distance along the horizontal meridian in the range of about 5-6 mm from the optical center.

11. The ophthalmic lens of any one of claims 1 to 10, wherein the vertical add power reaches a value of about 0.5 [D] at a radial distance within about 10 mm below the optical center along a vertical meridian.

12. The ophthalmic lens of any one of claims 1 to 11, wherein the vertical add power reaches a value in the range of about 0.50-1.00 [D] at a radial distance of about 9-15 mm below the optical center along the vertical meridian.

13. The ophthalmic lens of any one of claims 1 to 12, wherein the through focus add power reaches a value of about 2.5 [D] at a radial distance of about 25 degrees from the optical center along the horizontal meridian.

14. The ophthalmic lens of any one of claims 1 to 13, wherein the through focus add power reaches a value of about 3 [D] at a radial distance along the horizontal meridian within a range of about 30-35 degrees from the optical center.

15. The ophthalmic lens of any one of Claims 1 to 14, wherein the power profile is implemented by a posterior surface of the lens.

16. A method for designing at least one ophthalmic lens for influencing myopia progression, the method comprising: Obtain the subject's ophthalmic prescription; The vertical channel is configured to be substantially free of distortion, having a bottom apex defining a substantially U-shape and extending along a vertical meridian of the at least one ophthalmic lens to at least one of a bottom boundary and a top boundary of the ophthalmic lens, the vertical channel having: a first optical zone for providing a first optical power according to a specific prescription (Rx) for a corresponding eye, the first optical zone being disposed about an optical center of the at least one ophthalmic lens and extending to a top boundary of the ophthalmic lens; and a second optical zone for providing a vertical add power, the second optical zone being located at the bottom apex of the vertical channel; At least one through-focus zone is configured, at least partially surrounding the first optical zone, for providing a through-focus add power that extends substantially from an edge of the vertical channel and gradually changes in the temporal and nasal directions along a horizontal meridian to focus a distant image in front of a nasal peripheral retina and / or a temporal retina, respectively, and to minimize peripheral hyperopic defocus, wherein the through-focus add power reaches a predefined maximum value at a predefined distance from the optical center of the at least one ophthalmic lens.

17. The method of claim 16, further comprising measuring a specific prescription (Rx) for at least one eye.

18. The method of claim 16 or claim 17, wherein said configuring said at least one through-focus zone comprises determining a function indicative of a difference between said add power along a vertical meridian and a horizontal meridian of said ophthalmic lens.

19. The method of claim 18, wherein said determining said add power further comprises applying a linear fit to said function indicative of said difference between said add power along said vertical meridian and said horizontal meridian of said ophthalmic lens.

20. The method of any one of claims 16 to 19, further comprising providing a lens having the vertical channel including the first optical zone and the second optical zone.

21. A processing unit for providing a personalized lens optical property profile distribution, the processing unit comprising: a data entry tool configured and operable to receive a specific prescription (Rx) for an individual; data processing means configured and operable to determine a gradually varying optical add power in the temporal and nasal directions; and a data output tool configured and operable to provide a lens optical property profile distribution, the lens optical property profile distribution defining a vertical channel, the vertical channel being substantially free of distortion, extending from the optical center to at least one of the top and bottom boundaries of the lens, and including a first optical zone having an optical correction according to the Rx of the eye and a second optical zone for providing vertical additional light power.

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