Asymmetrically-partitioned surface micropore type defocus lens

Abstract

The invention belongs to the technical field of out-of-focus lenses, and particularly relates to an asymmetrically-partitioned surface micropore type out-of-focus lens which is provided with a plurality of optical partitions. A plurality of micropores are formed in each optical subarea, and each optical subarea is used for setting an area defocusing amount for the lens; according to the method and the device, the regional defocusing amount demand of the correction lens and the defocusing amount demand of refractive stagger increase are considered, the micropore array on the lens is subjected to optical partitioning, the defocusing amount of each optical partition is independently set based on the correction demand and / or the refractive stagger demand of different regions of the eyeball, and the adaptability and the correction effect of the defocusing lens are improved.

Description

TECHNICAL FIELD

[0001] The present application belongs to the technical field of defocus lenses, and particularly relates to a surface micropore type defocus lens with asymmetric partition. BACKGROUND

[0002] A defocus lens is a special designed optical lens, mainly used for controlling myopia progression (especially for children and adolescents), and its principle is to adjust the imaging position of light on the retina, reduce or offset the myopic defocus caused by the axial growth, so as to delay the deepening of myopia.

[0003] 1. Static limitations of traditional defocus lens design Static defocus and dynamic changes in eye axis are out of sync: the traditional lens adopts fixed defocus amount design (such as ±0.50D), which cannot adapt to the refractive disparity growth caused by the annual change of adolescent eye axis length (0.1-1.0mm / year). Studies have shown that the temporal defocus efficiency is more than 38% lower than the nasal side due to the fixed partition design, resulting in uneven myopia prevention and control effect.

[0004] Partition rigidity and field weight mismatch: the existing defocus lens adopts a rotationally symmetric structure, which cannot adapt to the asymmetric growth of the eyeball, for example, the temporal retina requires higher defocus, and the single defocus amount leads to imbalance in the correction of the nasal / temporal field of view, and the myopia control efficiency fluctuates by more than 30%. And it does not combine the high weight characteristics (accounting for ≥60%) of the actual 20° field angle of the macular area of the retina, resulting in a mismatch between the defocus energy distribution and the actual demand of the retina.

[0005] 2. Key defects of existing patent technology Freeform surface compensation mechanism is missing: for example, patent CN119002094A uses a freeform surface to compensate for refractive errors, but does not consider the influence of corneal asymmetry factor on defocus gradient, resulting in an adaptation deviation of corneal molding lens of ≥0.25D.

[0006] Insufficient data fusion: the existing technology does not combine the retinal morphology data with the scattering area distribution, resulting in insufficient matching degree of the microlens array of the lens and the physiological structure of the retina. SUMMARY

[0007] Therefore, the present application provides a surface micropore type defocus lens with asymmetric partition, which considers the regional defocus amount demand of the corrective lens and the defocus amount demand of the refractive disparity growth, and adjusts the micropore array on the lens in each optical partition based on the correction demand and / or refractive disparity demand of different regions of the eyeball, thereby improving the adaptability of the defocus lens to the eyeball and the correction effect.

[0008] In order to achieve the above technical purposes, the specific technical scheme adopted by the present application is as follows: An asymmetrically partitioned surface micropore type of defocus lens, the lens is provided with a plurality of optical partitions; each of the optical partitions is configured with a plurality of micropores, and each of the optical partitions is provided with a regional defocus amount for the lens; The overall defocus amount of the lens is asymmetrically arranged; Each of the optical partitions is used to adapt to the corrective defocus amount requirement and / or the adaptive defocus amount requirement of the refractive disparity growth of different regions of the eyeball; The factors for setting the defocus amount of each of the optical partitions include: The corneal asymmetric morphology factor of the eyeball, the axial length of the characteristic region of the retina, and / or the curvature of the retina.

[0009] Further, the lens adapts to the corrective defocus amount requirement and / or the adaptive defocus amount requirement of the refractive disparity growth in the following way: adaptively arranging the shape, diameter, depth, and density of each micropore in the optical partition corresponding to the region of the eyeball; the way in which the asymmetrically partitioned surface micropore type of defocus lens adapts to the refractive disparity growth includes: after the refractive disparity growth, the micropores in the corresponding optical partition are processed again.

[0010] Further, in order to quantify the defocus amount of each optical partition to adapt to the corrective lens, the defocus amount of the optical partition is set based on the following formula:

[0011] Wherein: is the positive defocus amount of the optical partition (i, j); AL is the axial length of the patient's eye; is the average axial length of the retina of the optical partition (i, j); Q is the value of the corneal asymmetric morphology factor; is the average curvature of the retina of the optical partition (i, j); , , And is a weight coefficient; The , , And The value range of is: , , , .

[0012] Further, in order to enable each optical partition to more comprehensively adapt to the correction of the eyeball, each of the optical partitions is obtained after being grid-divided based on the characteristics of the retinal topography map; the retinal topography map covers the macular fovea and its peripheral region of the human eye retina, or the optic disc edge region.

[0013] Furthermore, in order to reduce the design and manufacturing difficulty of each optical partition, the shape of the optical partition is fan-shaped, annular fan-shaped, or square; the number of optical partitions is 9-1000. Each of the optical partitions is provided with 20-2000 micropores; Furthermore, in order to facilitate optical control and ensure the stability of the defocusing effect, the micropores are cylindrical or hexagonal prisms in shape. Furthermore, in order to meet the defocus requirements between the temporal and nasal regions respectively, the micropore diameter of the optical partition in the temporal region of the lens is 20%-40% larger than that in the nasal region, and the micropore density of the optical partition in the temporal region is 30%-50% larger than that in the nasal region.

[0014] Furthermore, in order to facilitate optical control and ensure the stability of the defocusing effect, the diameter of the micropore unit is 0.12-1.2 mm.

[0015] Furthermore, in order to meet the defocus requirements between the temporal and nasal regions respectively, the micropore depth of the lens corresponding to the central region of the human eye is 100-150μm; The micropore depth of the lens corresponding to the central ring area of ​​the human eye is 150-250μm; The micropore depth of the lens corresponding to the outer ring area of ​​the human eye is 250-350μm.

[0016] By adopting the above technical solution, the present invention can also bring the following beneficial effects: This invention sets up multiple non-rotationally symmetric optical zones. Based on the regional defocus correction requirements of the human eye, the defocus amount of each zone is adaptively set, resulting in a better correction effect compared to existing defocus lenses. This invention integrates dynamic changes in axial length. When a patient's anisometropia changes, secondary processing can be performed on the corresponding zones based on the original lens without replacing the entire lens. This method can also adapt to the growth of anisometropia. Furthermore, it achieves precise matching by linking the dynamic model with human eye detection data, making the regional correction effect of defocused lenses more accurate. The partition boundaries of this invention are dynamically adjusted according to the refractive anisometropy (vertical difference ≥2.00D); at the same time, the micropore fractal reconstruction algorithm is optimized by combining the corneal asymmetry factor (Q value) and the field weight model, making the calculation of regional defocus more convenient. Attached Figure Description

[0017] To more clearly illustrate the technical solutions of the embodiments of this disclosure, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this disclosure. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0018] Figure 1 This is a schematic diagram of the surface structure of an asymmetric partitioned surface microporous defocusing lens according to a specific embodiment of the present invention; Figure 2 This is a schematic diagram of another asymmetric partitioned surface microporous defocusing lens in a specific embodiment of the present invention; Among them: 1. Lens; 2. Optical partition; 3. Micropores. Detailed Implementation

[0019] The embodiments of this disclosure will now be described in detail with reference to the accompanying drawings.

[0020] The following specific examples illustrate the implementation of this disclosure. Those skilled in the art can easily understand other advantages and effects of this disclosure from the content disclosed in this specification. Obviously, the described embodiments are only a part of the embodiments of this disclosure, and not all of them. This disclosure can also be implemented or applied through other different specific embodiments, and the details in this specification can also be modified or changed based on different viewpoints and applications without departing from the spirit of this disclosure. It should be noted that, in the absence of conflict, the following embodiments and features in the embodiments can be combined with each other. Based on the embodiments in this disclosure, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this disclosure.

[0021] It should be noted that various aspects of embodiments within the scope of the appended claims are described below. It will be apparent that the aspects described herein can be embodied in a wide variety of forms, and any particular structure and / or function described herein is merely illustrative. Based on this disclosure, those skilled in the art will understand that one aspect described herein can be implemented independently of any other aspect, and two or more of these aspects can be combined in various ways. For example, any number of aspects set forth herein can be used to implement the device and / or practice the method. Additionally, this device and / or method can be implemented using other structures and / or functionalities besides one or more of the aspects set forth herein.

[0022] It should also be noted that the illustrations provided in the following embodiments are only schematic representations of the basic concept of this disclosure. The illustrations only show the components related to this disclosure and are not drawn according to the number, shape and size of the components in actual implementation. In actual implementation, the form, quantity and proportion of each component can be arbitrarily changed, and the layout of the components may also be more complex.

[0023] Furthermore, specific details are provided in the following description to facilitate a thorough understanding of the examples. However, those skilled in the art will understand that the described aspects can be practiced without these specific details.

[0024] Traditional defocus lenses use a rotationally symmetrical micro-aperture array to simplify the human eye into a rotationally symmetrical imaging model for defocus correction. However, the defocus signal on the human retina is actually asymmetrically distributed. Under natural conditions, the temporal retina is more susceptible to hyperopic defocus, which stimulates axial elongation and exacerbates myopia development, thus requiring a larger amount of defocus. In contrast, the nasal retina experiences relatively less defocus, requiring less defocus. Existing defocus lenses do not take these factors into account, and the high weighting characteristic of the 20° field of view in the actual retinal macular region is also not considered. Therefore, the correction principle of existing defocus lenses has certain flaws.

[0025] In one embodiment of the present invention, an asymmetric partitioned surface microporous defocusing lens is provided, such as... Figures 1-2 As shown, the lens 1 is provided with multiple optical zones 2; each optical zone 2 is provided with multiple micropores 3, and each optical zone 2 is provided with a defocusing amount for the lens 1. The overall defocusing amount of the lens 1 is not rotationally symmetrically set; Each of the optical zones 2 is used to adapt to the corrective defocus requirements of different areas of the eyeball and / or the adaptive defocus requirements of the increase in anisometropia; The factors for setting the defocus amount of each optical zone 2 include: Corneal asymmetry morphology factors, axial length of characteristic retinal regions, and / or retinal curvature of the eyeball.

[0026] In this embodiment, multiple micropores 3 are provided on the optical partition 2. The micropores 3 are distributed on the surface of the lens 1. The surface micropores 3 can change the refractive index and predictably control the diffraction effect, thereby setting the defocus amount for the lens 1. The defocus amount is set in order to form an image in front of the retina, thereby providing the brain with a signal that "the axial length of the eye does not need to be elongated", thereby controlling the axial length of the eye to continue to elongate and achieving vision correction.

[0027] In this embodiment, each optical zone 2 can be divided according to the nasal and temporal sides, according to the macular field of view, by gridding, or by precisely dividing different areas according to the actual measured defocus amount requirements of the human eye; each optical zone 2 can be set with its own defocus amount, and the defocus amounts of these zones may be the same or different. This embodiment addresses anisometropia or axial elongation by performing secondary processing on the corresponding zones of the existing lens. Specific processing methods include adding new micropores and modifying existing micropores to alter their optical properties. This embodiment does not require replacing the entire lens, thereby achieving precise matching between the dynamic model and human eye detection data, making the regional correction effect of the defocused lens in this embodiment more accurate.

[0028] Compared to traditional defocus lenses, this embodiment fits the human eye into an asymmetric model that is closer to reality and has more biomimetic characteristics. It sets multiple defocus areas, thereby more accurately forming multiple defocus images, comprehensively suppressing further elongation of the axial length and enhancing correction efficiency.

[0029] Because the processing precision requirements of the micro-holes 3 on the defocus lens 1 in this embodiment are extremely high, the laser irradiation method offers extremely high processing efficiency and accuracy. This embodiment uses femtosecond laser processing for each optical zone 2, requiring digital quantification of the aforementioned asymmetric defocus requirements; otherwise, it cannot be implemented. This embodiment first sets a quantitative method: the adaptive defocus requirement of lens 1 to accommodate different regions' corrective defocus needs and / or the increasing anisometropia is achieved by adaptively arranging the shape, diameter, depth, and density of each micro-hole 3 in the corresponding optical zone 2 of the eye region. Secondly, the specific defocus amount of each optical zone 2 is quantified based on the following formula:

[0030] in: Δ is the positive defocusing amount of optical zone (i, j); AL is the patient's axial length. is the average axial length of the retina in optical region (i, j); Q is the corneal asymmetry morphology factor value; Let be the average retinal curvature of optical region (i, j); , , as well as These are the weighting coefficients; The , , as well as The range of values ​​for is: , , , .

[0031] The refractive power of optical zone 2 in this embodiment is:

[0032] in: For optical partition 2(i,j), the positive defocusing amount is given. The base refractive power for myopia correction of lens 1 ranges from -0.50D to -6.00D; The final refractive power of lens 1 is obtained by adding the defocus amount to the base refractive power. After obtaining the defocus amount requirement and refractive power of each optical zone 2, the density and aperture of the micropores during specific processing are achieved according to the calculation methods of existing technology, and this embodiment does not impose any limitations on this.

[0033] This embodiment sets weighting coefficients for axial length, average retinal axial length, corneal asymmetry morphology, and average retinal curvature to quantify specific defocus requirements, facilitating lens 1 design and femtosecond laser processing. The weighting coefficients are determined based on patient age, axial length, and the physician's clinical experience. For example, the α value is determined considering the patient's axial length or growth trend. , The weighting should also be determined based on the patient's specific condition, selecting a larger weighting value within the above range.

[0034] In this embodiment, in order to enable each optical zone 2 to more comprehensively adapt to eye correction, each optical zone 2 is obtained by gridding based on retinal topography features; the retinal topography covers the fovea centralis and its surrounding area or the edge area of ​​the optic disc in the human eye; in this embodiment, selecting the above two areas can enhance the consideration of the entire eyeball by the surface microporous defocus lens of the asymmetric partition in this embodiment, thereby enhancing the corrective effect of the defocus lens.

[0035] In some embodiments, in order to reduce the design and manufacturing difficulty of each optical partition 2, the present invention provides an optical partition 2 shape that is easy to manufacture and partition. The shape of the optical partition 2 is fan-shaped, annular fan-shaped, or square; the number of optical partitions 2 is 9-1000. Each of the optical partitions 2 is provided with 20-2000 micropores 3; In some embodiments, in order to facilitate optical control and ensure the stability of the defocusing effect, the micro-hole 3 is cylindrical or hexagonal prism in shape; In some embodiments, in order to meet the defocus requirements between the temporal and nasal regions respectively, the diameter of the micropores 3 in the optical partition 2 of the temporal region of the lens 1 is 20%-40% larger than that in the nasal region, and the density of the micropores 3 in the optical partition 2 of the temporal region is 30%-50% larger than that in the nasal region.

[0036] In some embodiments, to facilitate optical control and ensure the stability of the defocusing effect, the diameter of the micropore 3 unit is 0.12-1.2 mm. This size is suitable for the unique zoned defocusing requirements in the above embodiments. In this embodiment, to meet the defocusing requirements between the temporal and nasal regions respectively, the density of micropores 3 in the nasal region of the lens 1 is less than that in the temporal region, and the diameter is also smaller in the temporal region.

[0037] The depth of the micropore 3 in the lens 1 corresponding to the central area of ​​the human eye is 100-150μm; The depth of the micropore 3 in the lens 1 corresponding to the middle ring area of ​​the human eye is 150-250μm; The depth of the micropore 3 in the lens 1 corresponding to the outer ring area of ​​the human eye is 250-350μm; To meet certain special needs, micropores may not be provided in certain areas (such as the central area of ​​the human eye). If micropores are provided, the depth of micropore 3 shall be designed in accordance with the above guidelines.

[0038] The following further explains the simplified lens design based on zone 9, such as... Figure 1 As shown, the nine optical zones 2 include a central circle (corresponding to the central area of ​​the eyeball) and eight annular sectors set outside the central circle. The nine optical zones 2 together form a circular structure.

[0039] 1. Retinal data simplification and partition definition.

[0040] Data source: Curvature grid: Extract the average curvature value (mm) of 9 uniform regions at the center of the eyeball. - ¹).

[0041] Top left area: 0.79; Top area: 0.80; Top right area: 0.75; Left area: 0.66; Center area: 0.57; Right area: 0.82; Bottom left area: 0.85; Bottom area: 0.70; Bottom right area: 0.58 Value ).

[0042] Axial length mesh: Extract the average axial length (mm) of the corresponding region.

[0043] Top left area: 23 Top area: 22 Top right area: 22 Left area: 23 Center area: 24 Right area: 23 Bottom left area: 22 Bottom area: 23 Bottom right area: 22 Value ); Patient baseline parameters: total axial length =24.3mm; cornea value =-0.35; the patient's baseline refractive error when wearing lens 1. =-4.00D.

[0044] 2. Calculation of defocus amount in the 9 feature areas. formula:

[0045] Pick , , , This weighting factor takes into account subsequent axial length growth or anisometropia changes and is suitable for adolescents during their rapid growth period.

[0046] Value Explanation: To ensure the visual effect of lens 1, defocusing is not designed in the central area (e.g., Figure 1 (The central area shown does not have micropores). The data of the central area is omitted during the calculation. For ease of display, the remaining 8 feature areas are merged into four areas (adjacent areas are merged, the upper left area and the upper area are merged into a new upper left area, the lower left area and the left area are merged into a new lower left area, the upper right area and the upper area are merged into a new upper right area, and the lower right area and the lower area are merged into a new lower right area). The arithmetic mean is used for calculation. The calculation process and results are shown in Table 1.

[0047] Table 1. Calculation process and results of defocusing amount in the feature area.

[0048] 3. Clinical application. After the patient data is collected, micropores 3 in each optical zone 2 are processed on the basis of the above parameters. After processing is completed, the patient wears the lens. Initial results: Corrected visual acuity: Right eye 1.0, Left eye 1.0 (5-meter standard); Defocus achievement rate: Measured in the upper left area. The error compared with the design value is within ±0.2D. Six months later: Taking a patient's axial length increase of 0.15mm as an example (lower than the 0.41mm increase in the group without defocus intervention), the additional depth in the upper left region was +25μm. Following the patient's data, the parameters of the asymmetric partition surface microporous defocus lens were recalculated, resulting in an increase in ΔD to +2.05D. Based on the above verification process, it is clear that the corrective effect of this embodiment is significantly superior to traditional defocus lenses.

[0049] The above description is merely a specific embodiment of this disclosure, but the scope of protection of this disclosure is not limited thereto. Any variations or substitutions that can be easily conceived by those skilled in the art within the scope of the technology disclosed in this disclosure should be included within the scope of protection of this disclosure. Therefore, the scope of protection of this disclosure should be determined by the scope of the claims.

Claims

1. A surface microporous defocusing lens with asymmetrical partitioning, characterized in that, The lens is provided with multiple optical zones; each optical zone is provided with multiple micropores, and each optical zone is used to set the defocusing amount of the lens area. The overall defocusing amount of the lens is not rotationally symmetrically set; Each of the aforementioned optical zones is used to adapt to the corrective defocus requirements of different areas of the eyeball and / or the adaptive defocus requirements of increasing anisometropia; The factors for setting the defocus amount of each optical zone include: corneal asymmetry morphology factor of the eyeball, axial length of retinal characteristic regions and / or retinal curvature.

2. The asymmetric partitioned surface microporous defocusing lens according to claim 1, characterized in that, The way the lens adapts to the defocus requirements of different regions and / or the adaptive defocus requirements of anisometropia growth is by: adaptively arranging the shape, diameter, depth and density of each micropore in the corresponding optical zone of the eyeball region; The asymmetric partition surface microporous defocus lens adapts to the growth of refractive anisometropia by: after the refractive anisometropia grows, performing secondary processing on each of the micropores in the corresponding optical partition or adding micropores to the corresponding optical partition.

3. The asymmetric partitioned surface microporous defocus lens according to claim 2, characterized in that, The defocus amount of the optical zone is set based on the following formula: in: Δ is the positive defocusing amount of optical zone (i, j); AL is the patient's axial length. is the average axial length of the retina in optical region (i, j); Q is the corneal asymmetry morphology factor value; Let be the average retinal curvature of optical region (i, j); , , as well as These are the weighting coefficients; The , , as well as The range of values ​​for is: , , , .

4. The asymmetric partitioned surface microporous defocusing lens according to claim 1, characterized in that, Each optical partition is obtained by gridding based on retinal topographic map features; the retinal topographic map covers the fovea centralis and its surrounding area or the edge area of ​​the optic disc in the human eye.

5. The asymmetric partitioned surface microporous defocusing lens according to claim 1, characterized in that, The shape of the optical partition is fan-shaped, annular fan-shaped, or square; the number of optical partitions is 9-1000; each optical partition is provided with 20-2000 micropores.

6. The asymmetric partitioned surface microporous defocusing lens according to claim 1, characterized in that, The micropores are cylindrical or hexagonal prisms.

7. The asymmetric partitioned surface microporous defocusing lens according to claim 1, characterized in that, On the lens: the micropore diameter of the optical zone in the temporal region is 20%-40% larger than that in the nasal region, and the micropore density of the optical zone in the temporal region is 30%-50% larger than that in the nasal region.

8. The asymmetric partitioned surface microporous defocusing lens according to claim 7, characterized in that, The diameter of the microporous unit is 0.12-1.2 mm.

9. The asymmetric partitioned surface microporous defocusing lens according to claim 8, characterized in that, The micropore depth of the lens corresponding to the central area of ​​the human eye is 100-150μm; The micropore depth of the lens corresponding to the central ring area of ​​the human eye is 150-250μm; The micropore depth of the lens corresponding to the outer ring area of ​​the human eye is 250-350μm.

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