Ophthalmic lens

Abstract

The utility model provides an ophthalmic lens, and relates to the technical field of ophthalmic optics. An optical part of the lens has a geometric center, and the focal power of any point of the optical part and the focal power of the geometric center meet one of the following conditions: the focal power of any point of the optical part is greater than the focal power of the geometric center; the focal power of any point of the optical part is smaller than that of the geometric center; the focal power of partial points of the optical part is greater than the focal power of the geometric center, and the focal power of the rest points is equal to the focal power of the geometric center; the focal power of partial points of the optical part is smaller than the focal power of the geometric center, and the focal power of the remaining points is equal to the focal power of the geometric center. The focal power on the circumference is continuously distributed along the circumference at any radius by taking the geometric center as the circle center, and the distribution trends of the focal power on at least two angles along the radius are different, so that the lens is better matched with the field angle of the lens, and the lens defocusing amounts of different angles in the corresponding field angle range are basically the same.

Description

Technical Field

[0001] This invention relates to the field of optometry, and more particularly to an ophthalmic lens. Background Technology

[0002] The field of view of the human eye varies at different angles. When looking straight ahead (without considering eye movement), the upper field of view is generally about 10°, and the lower field of view is about 15°. Taking eye movement into account, the upper field of view is generally about 50°, the lower field of view is about 70°, the nasal field of view is about 60°, and the temporal field of view is about 100°.

[0003] Due to the different field of view, the optical zones of the lenses used for ophthalmic lenses that vary with the field of view (such as contact lenses worn outside the eye, intraocular lenses implanted with phakic lenses and aphakic lenses) are different. That is, the optical zone of the lens used above is smaller than that below, and the optical zone of the lens used on the nasal side is smaller than that on the temporal side.

[0004] The field of view has a relatively small impact on monofocal lenses, but a larger impact on graduated or multifocal lenses. Existing lenses do not consider the influence of the field of view, and the optical power distribution relative to the geometric center of the lens has a 360° symmetrical structure. Summary of the Invention

[0005] This invention provides an ophthalmic lens to address the shortcomings of existing technologies that do not consider the influence of the field of view. The existing technology features a 360° symmetrical optical power distribution relative to the geometric center of the lens, which leads to uneven focusing of light in different directions. In areas with a large field of view, the light may not focus uniformly, resulting in aberrations and visual interference, affecting the clarity and comfort of the visual experience. Furthermore, the 360° symmetrical lens design may be difficult to accurately position during wear, potentially causing the lens to fail to quickly return to the optimal matching position when rotating or moving within the eye, affecting the stability and comfort of wearing the lens.

[0006] This invention provides an ophthalmic lens, wherein the optical portion of the lens has a geometric center, and the optical power at any point of the optical portion satisfies one of the following conditions relative to the optical power at the geometric center: the optical power at any point of the optical portion is greater than the optical power at the geometric center; the optical power at any point of the optical portion is less than the optical power at the geometric center; the optical power at some points of the optical portion is greater than the optical power at the geometric center, and the optical power at the remaining points is equal to the optical power at the geometric center; the optical power at some points of the optical portion is less than the optical power at the geometric center, and the optical power at the remaining points is equal to the optical power at the geometric center.

[0007] Within the optical section, the optical power is continuously distributed along the circumference of a circle with the geometric center as the center and any radius, and there are at least two angles where the optical power distribution along the radius has different trends.

[0008] According to the present invention, an ophthalmic lens, within the optical section of diameter D, displays a curve showing the change in optical power as a function of angle on the circumference corresponding to any radius r. Continuously differentiable, where θ∈[0°, 360°), r∈(0, D / 2).

[0009] According to the present invention, an ophthalmic lens has at least two angles θ1 and θ2, and the radial power of the lens corresponding to angle θ1 varies with the radius. Curve of radial optical power as a function of radius corresponding to angle θ2 They are not the same, where θ1∈[0°, 360°), θ2∈[0°, 360°), and r∈(0, D / 2).

[0010] According to an ophthalmic lens provided by the present invention, within the range of the optical part, there is at least one optical power variation curve as a function of angle on the circumference corresponding to a radius r1. It is not a constant value, where θ∈[0°, 360°), r1∈(0, D / 2).

[0011] According to the present invention, an ophthalmic lens has a sector whose vertex coincides with the geometric center, and the optical power changes with angle on any circle r within the sector, conforming to the trend of a sine function.

[0012] According to an ophthalmic lens provided by the present invention, within the scope of the optical section, the optical power distribution trends of the two radii are not the same along at least one diameter passing through the geometric center; and along the remaining diameters passing through the geometric center, the optical power distribution trends of the two radii are symmetrical about the geometric center, i.e.: , r∈(0, D / 2], θ∈[0°, 180°), and θ is not equal to the direction of the diameter where the optical power distribution trend is different.

[0013] According to the ophthalmic lens provided by the present invention, within a semicircular range formed by 0°-180°, the optical power variation curves with radius for any angles θ1 and θ2 are not the same, i.e. Where θ∈(0°, 180°), r∈(0, D / 2).

[0014] According to the ophthalmic lens provided by the present invention, the optical power on the semicircle corresponding to any radius r changes with the angle in a trend that conforms to... , where θ∈(0°, 180°), r∈(0, D / 2], and a and b are constants.

[0015] According to the present invention, the optical power of an ophthalmic lens on a semicircle corresponding to any radius r varies with the angle according to the following formula (1).

[0016] (1)

[0017] Where r∈(0, D / 2], , It is a constant. .

[0018] According to the ophthalmic lens provided by the present invention, the optical power on the semicircle corresponding to any radius r changes with the angle in accordance with the following formula (2).

[0019] (2)

[0020] Where r∈(0, D / 2], , It is a constant. .

[0021] According to the present invention, the radial optical power of an ophthalmic lens at any angle θ varies with the radius. Continuously differentiable, where θ∈[0°, 360°), r∈(0, D / 2).

[0022] According to the present invention, an ophthalmic lens includes a contact lens, which is a corneal contact lens or a scleral contact lens, and the diameter of the optical part of the corneal contact lens and the optical part of the scleral contact lens are both 6-12 mm.

[0023] According to the present invention, an ophthalmic lens is provided, the lens comprising an intraocular phakic intraocular lens, wherein the diameter of the optical portion of the intraocular phakic intraocular lens is 4-8 mm.

[0024] According to the present invention, an ophthalmic lens is a progressive focal length contact lens used for myopic patients to simultaneously slow down the progression of myopia. The rear surface of the lens is spherical, and the front surface of the lens is aspherical.

[0025] According to the present invention, an ophthalmic lens is a phakic intraocular lens used to relieve eye strain to a certain extent. The rear surface of the lens is aspherical, and its front surface is aspherical.

[0026] According to the present invention, an ophthalmic lens is an aphakic intraocular lens used to extend the depth of field, wherein the rear surface of the lens is spherical and the front surface of the lens is aspherical.

[0027] According to the present invention, an ophthalmic lens is provided, the lens comprising an aphakic intraocular lens, wherein the diameter of the optical portion of the aphakic intraocular lens is 4-8 mm.

[0028] According to an ophthalmic lens provided by the present invention, the optical part of the contact lens includes a central correction zone centered on the geometric center and a defocus zone surrounding the central correction zone. The optical power at any point within the central correction zone is equal, the optical power of the defocus zone is greater than or equal to the optical power of the central correction zone, and the optical power distribution trend along the radius of the defocus zone is different at at least two angles.

[0029] According to an ophthalmic lens provided by the present invention, the diameter of the optical part of the contact lens is 6-12 mm, and the diameter of the central correction zone is 1-3.5 mm.

[0030] According to an ophthalmic lens provided by the present invention, the optical power at any angle within the defocus zone varies with the radius as a function of the radius and is continuously differentiable.

[0031] According to an ophthalmic lens provided by the present invention, the defocused area has a non-continuous curve of optical power versus radius at at least one angle.

[0032] According to an ophthalmic lens provided by the present invention, the optical power at any angle of the defocus area gradually increases with the radius, or the rate of change of the optical power at any angle of the defocus area with the radius is continuous and first increases and then decreases, and the rate of change is not 0.

[0033] According to an ophthalmic lens provided by the present invention, the change rate curve of optical power at any angle of the defocus zone with respect to radius is uniform.

[0034] According to an ophthalmic lens provided by the present invention, the defocused area has at least one discontinuous curve of the rate of change of optical power with radius at an angle.

[0035] According to the present invention, an ophthalmic lens has a positioning structure that positions the lens circumferentially relative to the eyeball when worn or after implantation in the human eye.

[0036] According to an ophthalmic lens provided by the present invention, the positioning structure includes a weight-bearing portion disposed in the peripheral area around the optical zone, and the weight-bearing portions of the plurality of lenses have different relative positions in the circumferential direction.

[0037] According to an ophthalmic lens provided by the present invention, the weight-bearing portion is formed by providing a thickened region in the peripheral area.

[0038] According to an ophthalmic lens provided by the present invention, the weight-bearing portion is disposed on the edge portion of the lens, and the number of the weight-bearing portions is one or more, and the plurality of weight-bearing portions are symmetrically arranged. The shape of the weight-bearing portion is fan-shaped, annular, crescent-shaped, circular or flattened.

[0039] According to an ophthalmic lens provided by the present invention, the weight-bearing portion extends circumferentially, and the circumferential range is 10°-180°, 20°-140°, or 30°-110°.

[0040] According to an ophthalmic lens provided by the present invention, the major axis of a plurality of elliptical weight-bearing portions extends along the circumference of the lens, and the minor axis extends along the radial direction of the lens.

[0041] According to an ophthalmic lens provided by the present invention, the positioning structure includes a thickening region and a thinning region, the thickening region and the thinning region being located on the same diameter of the contact lens, and the thickening region and the thinning region being disposed opposite to each other on both sides of the center of the contact lens.

[0042] According to an ophthalmic lens provided by the present invention, the thickened area has a circumferential range of 50°-130°, 65°-115°, or 80°-100°.

[0043] According to an ophthalmic lens provided by the present invention, the thinning area has a circumferential range of 50°-130°, 65°-115°, or 80°-100°.

[0044] According to an ophthalmic lens provided by the present invention, the thickened region and the thinned region are asymmetrically distributed.

[0045] According to an ophthalmic lens provided by the present invention, the thickness of the peripheral region gradually decreases along the length of one diameter of the contact lens, thereby forming the positioning structure.

[0046] According to an ophthalmic lens provided by the present invention, the positioning structure includes at least two thinning regions, the two thinning regions being located on the same diameter of the contact lens, and the two thinning regions being arranged opposite to each other on both sides of the center of the contact lens.

[0047] The ophthalmic lens provided by this invention, by ensuring a continuous distribution of optical power along the circumference of a circle with an arbitrary radius centered on the geometric center, and with at least two angles exhibiting different distribution trends along the radius, allows the lens to better match its field of view. The defocus amount of the lens is essentially the same at different angles within the corresponding field of view. Matching the lens area in each direction with the corresponding field of view avoids waste and insufficient effect, prevents abrupt changes in optical power, and ensures a smooth transition of light when the lens rotates or the eye moves, preventing visual interference or aberrations caused by sudden changes in optical power, thus providing the user with a more natural and comfortable visual experience. Furthermore, the ophthalmic lens provided by this invention, due to its circumferential positioning structure, ensures the lens remains stable during wear, preventing arbitrary rotation or displacement. Users do not need to frequently adjust or worry about lens displacement during various activities, thus enabling more natural and comfortable use of the lens. Attached Figure Description

[0048] To more clearly illustrate the technical solutions in this invention or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are some embodiments of this invention. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0049] Figure 1 This is one of the schematic diagrams of the optical power of a lens as a function of its radius in the prior art.

[0050] Figure 2 This is one of the schematic diagrams of the optical power variation curve with radius provided by the present invention.

[0051] Figure 3 This is one of the three-dimensional schematic diagrams illustrating the trend of optical power variation of the lens provided by the present invention.

[0052] Figure 4 This is one of the top-view schematic diagrams showing the trend of optical power variation of the lens provided by the present invention.

[0053] Figure 5 This is one of the schematic diagrams of the optical power variation curve with angle provided by the present invention.

[0054] Figure 6 This is one of the schematic diagrams of the curves showing the change of optical power with radius at several specific angles provided by the present invention.

[0055] Figure 7 This is one of the schematic diagrams showing the positional relationship of radii corresponding to several specific angles provided by the present invention.

[0056] Figure 8This is one of the schematic diagrams showing the rate of change of optical power with radius at several specific angles provided by the present invention.

[0057] Figure 9 This is a schematic diagram of the lens structure provided by the present invention.

[0058] Figure 10 This is the second schematic diagram of the curve of the optical power of a lens changing with its radius in the prior art.

[0059] Figure 11 This is the second schematic diagram of the optical power variation curve with radius provided by the present invention.

[0060] Figure 12 This is the second three-dimensional schematic diagram of the optical power variation trend of the lens provided by the present invention.

[0061] Figure 13 This is the second top-view schematic diagram of the optical power variation trend of the lens provided by the present invention.

[0062] Figure 14 This is the second schematic diagram of the optical power variation curve with angle provided by the present invention.

[0063] Figure 15 This is the second schematic diagram of the curves showing the change of optical power with radius at several specific angles provided by this invention.

[0064] Figure 16 This is the second schematic diagram showing the positional relationship of radii corresponding to several specific angles provided by this invention.

[0065] Figure 17 This is the second of several schematic diagrams illustrating the rate of change of optical power with radius at specific angles provided by this invention.

[0066] Figure 18 This is the third schematic diagram of the curve showing the change of optical power of a lens with radius in the prior art.

[0067] Figure 19 This is the third schematic diagram of the optical power variation curve with radius provided by the present invention.

[0068] Figure 20 This is the third three-dimensional schematic diagram of the optical power variation trend of the lens provided by the present invention.

[0069] Figure 21 This is the third top-view schematic diagram of the optical power variation trend of the lens provided by the present invention.

[0070] Figure 22 This is the third schematic diagram of the optical power variation curve provided by the present invention.

[0071] Figure 23 This is the third of several schematic diagrams showing the variation curves of optical power with radius at specific angles provided by this invention.

[0072] Figure 24 This is the third of several schematic diagrams showing the positional relationship of radii corresponding to specific angles provided by this invention.

[0073] Figure 25 This is the fourth schematic diagram of the curve of the optical power of a lens changing with its radius in the prior art.

[0074] Figure 26 This is the fourth schematic diagram of the curve showing the change of optical power with radius provided by the present invention.

[0075] Figure 27 This is the fourth schematic diagram of the optical power variation curve provided by the present invention.

[0076] Figure 28 This is the fourth of several schematic diagrams showing the variation curves of optical power with radius at specific angles provided by this invention.

[0077] Figure 29 This is the fourth of several schematic diagrams showing the positional relationship of radii corresponding to specific angles provided by this invention.

[0078] Figure 30 This is the fifth schematic diagram of the optical power of a lens as a function of its radius in the prior art.

[0079] Figure 31 This is the fifth schematic diagram of the curve showing the change of optical power with radius provided by the present invention.

[0080] Figure 32 This is the fifth schematic diagram of the optical power variation curve provided by the present invention.

[0081] Figure 33 This is the fifth of several schematic diagrams showing the variation curves of optical power with radius at specific angles provided by this invention.

[0082] Figure 34 This is the fifth of several schematic diagrams showing the positional relationships of radii corresponding to specific angles provided by this invention.

[0083] Figure 35 This is one of the structural schematic diagrams of the contact lens provided by the present invention.

[0084] Figure 36 This is the second schematic diagram of the contact lens provided by the present invention.

[0085] Figure 37 This is the third schematic diagram of the contact lens provided by the present invention.

[0086] Figure 38 This is the fourth schematic diagram of the contact lens provided by the present invention.

[0087] Figure 39This is the fifth schematic diagram of the contact lens provided by the present invention.

[0088] Figure 40 This is the sixth schematic diagram of the contact mirror provided by the present invention.

[0089] Figure 41 This is the seventh schematic diagram of the contact lens provided by the present invention.

[0090] Figure 42 This is the eighth schematic diagram of the contact mirror provided by the present invention.

[0091] Figure 43 yes Figure 42 A schematic diagram of the cross-section along section line AA.

[0092] Figure 44 yes Figure 42 A schematic diagram of the cross-section along section line BB.

[0093] Figure 45 This is the ninth schematic diagram of the contact lens provided by the present invention.

[0094] Reference numerals: 1. Optical section; 2. Peripheral area; 3. Weight section; 6. Thickened area; 7. Thinned area; 8. Lens. Detailed Implementation

[0095] To make the objectives, technical solutions, and advantages of this invention clearer, the technical solutions of this invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of this invention. All other embodiments obtained by those skilled in the art based on the embodiments of this invention without creative effort are within the scope of protection of this invention.

[0096] In the description of the embodiments of the present invention, it should be noted that the terms "center," "longitudinal," "lateral," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing the embodiments of the present invention and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on the embodiments of the present invention. In addition, the terms "first," "second," and "third" are used for descriptive purposes only and should not be construed as indicating or implying relative importance.

[0097] In the description of the embodiments of the present invention, it should be noted that, unless otherwise explicitly specified and limited, the terms "connected" and "linked" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium. Those skilled in the art can understand the specific meaning of the above terms in the embodiments of the present invention based on the specific circumstances.

[0098] In embodiments of the present invention, unless otherwise explicitly specified and limited, "above" or "below" the second feature can mean that the first feature is in direct contact with the second feature, or that the first feature is in indirect contact with the second feature through an intermediate medium. Furthermore, "above," "on top of," and "over" the second feature can mean that the first feature is directly above or diagonally above the second feature, or simply that the first feature is at a higher horizontal level than the second feature. "Below," "below," and "under" the second feature can mean that the first feature is directly below or diagonally below the second feature, or simply that the first feature is at a lower horizontal level than the second feature.

[0099] In the description of this specification, the references to terms such as "one embodiment," "some embodiments," "example," "specific example," or "some examples," etc., refer to specific features, structures, materials, or characteristics described in connection with that embodiment or example, which are included in at least one embodiment or example of the present invention. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples. Moreover, without contradiction, those skilled in the art can combine and integrate the different embodiments or examples described in this specification, as well as the features of different embodiments or examples.

[0100] A first aspect of the present invention provides an ophthalmic lens, wherein the optical part 1 of the lens has a geometric center, and the optical power of any point of the optical part 1 and the optical power of the geometric center satisfy one of the following conditions: the optical power of any point of the optical part 1 is greater than the optical power of the geometric center; the optical power of any point of the optical part 1 is less than the optical power of the geometric center; the optical power of some points of the optical part 1 is greater than the optical power of the geometric center, and the optical power of the remaining points is equal to the optical power of the geometric center; the optical power of some points of the optical part 1 is less than the optical power of the geometric center, and the optical power of the remaining points is equal to the optical power of the geometric center.

[0101] Within the optical section 1, the optical power distribution along the circumference is continuous with the geometric center as the center and with any radius, and there are at least two angles where the optical power distribution along the radius has different trends.

[0102] The ophthalmic lens provided by this invention achieves a continuous distribution of optical power along the circumference of a circle with an arbitrary radius centered on the geometric center. Furthermore, at least two angles exhibit different distribution trends along the radius, allowing the lens to better match its field of view. The defocus amount of the lens is essentially the same at different angles within the corresponding field of view, ensuring that the lens area in each direction matches the corresponding field of view. This avoids waste and insufficient effect, prevents abrupt changes in optical power, and ensures a smooth transition of light when the lens rotates or the eye moves, preventing visual interference or aberrations caused by sudden changes in optical power. This provides users with a more natural and comfortable visual experience. In addition, the ophthalmic lens provided by this invention has a positioning structure that positions the lens circumferentially. This positioning structure ensures that the lens remains stable during wear, preventing arbitrary rotation or displacement. Users do not need to frequently adjust or worry about lens displacement during various activities, allowing for more natural and comfortable lens use.

[0103] It should be noted that in this invention, any point of the optical part 1 refers to any point other than the geometric center.

[0104] In one embodiment of the present invention, within the area of ​​the optical part 1 with a diameter of D (in this embodiment, the optical part 1 is a circular region with a diameter of D), the optical power variation curve of the circumference corresponding to any radius r with respect to angle is shown. Continuously differentiable, where θ∈[0°, 360°), r∈(0, D / 2). This is achieved by plotting the optical power as a function of angle on a circle corresponding to any radius r. Continuous doubling ensures the performance stability and imaging quality of ophthalmic lenses during zooming.

[0105] In one embodiment of the present invention, within the area of ​​the optical unit 1, there are at least two angles θ1 and θ2, the magnitudes of angles θ1 and θ2 are different, and the radial optical power corresponding to angle θ1 varies with the radius. Curve of radial optical power as a function of radius corresponding to angle θ2 They are not the same, where θ1∈[0°, 360°), θ2∈[0°, 360°), and r∈(0, D / 2). This is achieved by making the radial optical power corresponding to angle θ1 vary with the radius. Curve of radial optical power as a function of radius corresponding to angle θ2 Different focal lengths allow for variations in the optical power of different areas of the ophthalmic lens, resulting in optimal visual effects and image quality.

[0106] It should be noted that each angle θ has its own radius, and the radial optical power corresponding to angle θ refers to the optical power over a radius of angle θ.

[0107] In one embodiment of the present invention, within the scope of the optical unit, there is at least one curve showing the change in optical power as a function of angle on the circumference corresponding to a radius r1. The values ​​are not constants, where θ∈[0°, 360°) and r1∈(0, D / 2). This design enables the optical power of the ophthalmic lens to be distributed according to the design requirements, achieving optimal visual effect and image quality.

[0108] In one embodiment of the invention, a sector is provided with its vertex coinciding with the geometric center. Within the sector, on any circle corresponding to an angle r, the optical power varies with angle in accordance with the trend of a sine function. This design provides a continuous field of view and a comfortable visual experience. Since the sine function is a known function, it will not be described in detail here.

[0109] In one embodiment of the present invention, within the scope of the optical unit, on a diameter passing through the geometric center, the optical power distribution trends of the two radii constituting that diameter are not identical. Of course, the number of such diameters is not limited to one; it can also be two, three, or more. On the remaining diameters passing through the geometric center, the optical power distribution trends of the two radii are symmetrical about the geometric center, that is: , r∈(0, D / 2], θ∈[0°, 180°), and θ is not equal to the direction of the diameters with different optical power distribution trends. By making the optical power distribution trends of the remaining few diameters passing through the geometric center symmetrical about the geometric center with respect to the radius distribution trend, not only is the design process simplified, but it also helps to improve the performance and imaging quality of ophthalmic lenses.

[0110] In one embodiment of the present invention, within the semicircle range of 0°-180°, the optical power variation curves with radius for any angles θ1 and θ2 are not the same, i.e. Where θ∈(0°, 180°), r∈(0, D / 2).

[0111] In one embodiment of the present invention, the trend of optical power variation with angle on the semicircle corresponding to any radius r conforms to... , where θ∈(0°, 180°), r∈(0, D / 2], and a and b are constants.

[0112] In one embodiment of the present invention, the optical power variation curve of the semicircle corresponding to any radius r with respect to the angle conforms to the following formula (1).

[0113] (1)

[0114] Where r∈(0, D / 2], , It is a constant. .

[0115] In one embodiment of the present invention, the optical power on the semicircle corresponding to any radius r changes with the angle according to the following formula (2).

[0116] (2)

[0117] Where r∈(0, D / 2], , It is a constant. .

[0118] In one embodiment of the present invention, the radial optical power variation curve corresponding to any angle θ is shown as a function of radius. Continuously differentiable, where θ∈[0°, 360°), r∈(0, D / 2).

[0119] In one embodiment of the present invention, the lens includes a contact lens, which is a corneal contact lens or a scleral contact lens, and the diameter of the optical part of the corneal contact lens and the optical part of the scleral contact lens are both 7-12mm.

[0120] In one embodiment of the present invention, the lens includes an intraocular phakic intraocular lens, and the diameter of the optical part of the intraocular phakic intraocular lens is 4-8 mm.

[0121] In one embodiment of the present invention, the lens includes an aphakic intraocular lens, the diameter of which is 4-8 mm.

[0122] In one embodiment of the present invention, the lens includes an external contact lens. The optical part of the contact lens includes a central correction zone centered on the geometric center and a defocus zone surrounding the central correction zone. The defocus zone is annular. The optical power at any point in the central correction zone is equal. The optical power of the defocus zone is greater than or equal to the optical power of the central correction zone. Furthermore, the optical power distribution trend along the radius is different at at least two angles in the defocus zone.

[0123] In one embodiment of the present invention, the diameter of the optical part of the contact lens is 7-12 mm.

[0124] In one embodiment of the present invention, the diameter of the central correction zone is 1.5-3.5 mm.

[0125] In one embodiment of the present invention, the optical power at any angle within the defocus zone varies with the radius as a function of the radius and is continuously differentiable.

[0126] In one embodiment of the present invention, the defocused region has a non-continuous curve of optical power versus radius at at least one angle.

[0127] In one embodiment of the present invention, the optical power at any angle of the defocused area gradually increases with the radius, or the rate of change of the optical power at any angle of the defocused area with the radius is continuous and first increases and then decreases, and the rate of change is not 0.

[0128] In one embodiment of the present invention, the rate of change of optical power with radius at any angle in the defocused region is uniform.

[0129] In one embodiment of the present invention, the defocused region has at least one discontinuous curve of the rate of change of angular optical power with radius.

[0130] In one embodiment of the invention, the lens has a positioning structure that positions it circumferentially relative to the eyeball when worn or after implantation in the human eye.

[0131] In one embodiment of the present invention, the positioning structure includes a weighted portion disposed in the peripheral area around the optical area, and the weighted portions of the multiple lenses are positioned differently in the circumferential direction.

[0132] In one embodiment of the present invention, the weight-bearing portion is formed by providing a thickened region in the peripheral area.

[0133] In one embodiment of the present invention, the weight-bearing part is disposed on the edge of the lens, and the number of weight-bearing parts is one or more, and the multiple weight-bearing parts are symmetrically arranged. The shape of the weight-bearing parts is fan-shaped, crescent-shaped, circular, or flat-circular.

[0134] In one embodiment of the present invention, the weight-bearing portion extends circumferentially, and the circumferential range is 10°-180°, 20°-140°, or 30°-110°.

[0135] In one embodiment of the invention, the major axis of the plurality of elliptical vertical weights extends circumferentially along the lens, and the minor axis extends radially along the lens.

[0136] In one embodiment of the present invention, the positioning structure includes a thickened region and a thinned region, the thickened region and the thinned region being located on the same diameter of the contact lens, and the thickened region and the thinned region being arranged opposite to each other on both sides of the center of the contact lens.

[0137] In one embodiment of the present invention, the thickened area has a circumferential range of 50°-130°, 65°-115°, or 80°-100°.

[0138] In one embodiment of the present invention, the thinning region is 50°-130°, 65°-115° or 80°-100° in the circumferential direction.

[0139] In one embodiment of the present invention, the thickened region and the thinned region are asymmetrically distributed.

[0140] In one embodiment of the present invention, the thickness of the peripheral region gradually decreases along the length of one diameter of the contact mirror, thereby forming a positioning structure.

[0141] In one embodiment of the present invention, the positioning structure includes at least two thinning regions located on the same diameter of the contact mirror and disposed opposite to each other on both sides of the center of the contact mirror.

[0142] A second aspect of the present invention also provides a method for designing an ophthalmic lens, wherein the calculation method is applied to the ophthalmic lens described in any of the above embodiments, and the ophthalmic lens design method includes the following steps:

[0143] Step S100: Determine the field of view of the human eye;

[0144] Step S200: Determine the diameter of the optical part based on the field of view;

[0145] Step S300: Establish the lens coordinate system;

[0146] Step S400: Determine the curves of optical power versus radius for different field of view directions;

[0147] Step S500: Determine the curve of optical power versus angle on a semicircle corresponding to any radius r;

[0148] Step S600: Determine the trend of change in the optical power of the lens.

[0149] Example 1

[0150] In one specific embodiment of the present invention, the lens is a progressive focal length contact lens with a diameter of 10.6 mm. The lens is used for myopic patients to simultaneously slow the progression of myopia. The diameter of the optical part of the lens is 6.0 mm, and the vertex spherical power of the lens is -6.0D. The rear surface of the lens is spherical, and the front surface of the lens is aspherical. Figure 1 As shown, the lens in the prior art has a 360° rotationally symmetrical power distribution.

[0151] The following describes ophthalmic lens design methods in conjunction with the human eye's field of vision. These methods include:

[0152] In step S100, the upper field of view of the human eye is determined to be 5°, and the lower field of view of the human eye is determined to be 15°.

[0153] In step S200, based on the structural parameters of the human eye (such as corneal K-value, anterior chamber depth, pupil diameter, etc.), the radius of the optical part corresponding to the upper 5° field of view of the human eye is determined to be 2.5 mm, and the radius of the optical part corresponding to the lower 15° field of view is determined to be 3.0 mm, using the ray tracing method.

[0154] Step S300: Establish a coordinate system with the top of the lens defined as 90° and the bottom of the lens defined as 270°.

[0155] Step S400: Determine that a 5.0D defocus is achieved at a radius of 3.0mm for the field of view below the lens (270°), and a 5.0D defocus is achieved at a radius of 2.5mm for the field of view above the lens (90°). Then, calculate the curve of the optical power above the lens as a function of radius. The curve showing the change in optical power as a function of radius below the lens is modified. The transformation is performed, where r∈(0,3). For example... Figure 2 As shown, Figure 2 The figure illustrates the relationship between the radius of a lens and its optical power.

[0156] Step S500: Determine the curve of optical power as a function of angle on the semicircle corresponding to any radius r. The curve of optical power as a function of angle must satisfy the following formula (3).

[0157] (3)

[0158] Where θ∈[0°, 360°), r∈(0, 3).

[0159] Step S600, as follows Figures 3 to 5 As shown, the circumferential optical power of the lens changes continuously at any radius distance.

[0160] In this embodiment, the optical power at any point in the lens optics is greater than the optical power at the geometric center, or the optical power at some points in the optics is greater than the optical power at the geometric center, and the optical power at the remaining points is equal to the optical power at the geometric center. For example... Figure 6 As shown, Figure 6 The text lists several radii (0.5mm, 1.0mm, 1.5mm, 2.0mm, 2.5mm, 3.0mm) corresponding to the circumference of the circles, showing that the optical power as a function of angle is continuously differentiable and conforms to a sinusoidal trend. For example... Figure 7 and Figure 8 As shown, Figure 7 and Figure 8 The text lists several different angles (0°, 45°, 90°, 126°, 198°, 270°, 336°) and shows that the optical power variation curves with radius are not entirely the same. Furthermore, the optical power distribution trends with radius at the 90° and 270° radii are symmetrical about the geometric center. , where θ∈[0°, 180°), θ≠90, r∈(0, 3).

[0161] In this embodiment, the circular central region with a diameter of 2.0 mm is the central correction zone, and the annular region with a diameter of 2-6 mm is the defocus zone. The optical power at any angle in the defocus zone gradually increases with the radius, or the rate of change of optical power with the radius first increases and then decreases, and the rate of change is not zero. For example... Figure 8 As shown, the rate of change of optical power with radius is the same at different angles.

[0162] Furthermore, to facilitate positioning of the contact lens for external use, this embodiment also includes a peripheral area surrounding the outer periphery of the optical element, with a weighted structure and / or markings provided in the 270° direction of this peripheral area. For example... Figure 9 As shown, the position of the weighting structure is basically consistent with the location of the marking. Here, the weighting structure typically refers to a thickening of the lower part of the lens (i.e., the direction towards the center of the earth after wearing) to a certain extent, while the upper part of the lens is thinned. During wear, the lens is affected by gravity, and the thickest part ultimately remains at the bottom, creating a positioning effect. The thickened part is located outside the optical part of the lens. By setting this weighting structure and / or marking, the lens, after being worn outside the eye, better matches its field of view, and the defocus amount of the lens is basically the same within the corresponding field of view range at different angles.

[0163] Example 2

[0164] In another specific embodiment of the invention, the lens is a progressive focal length contact lens with a diameter of 14.0 mm. The lens is used for myopic patients to simultaneously slow the progression of myopia; the diameter of the optical part is 8.0 mm, and the vertex spherical power of the lens is -6.0D. The rear surface of the lens is spherical, and the front surface of the lens is aspherical. Figure 10 As shown, in the prior art, the lens has a 360° rotationally symmetrical optical power distribution.

[0165] The following describes ophthalmic lens design methods in conjunction with the human eye's field of vision. These methods include:

[0166] In step S100, the upper field of view of the human eye is determined to be 50°, the lower field of view of the human eye is determined to be 70°, the nasal field of view is determined to be 60°, and the temporal field of view is determined to be 100°.

[0167] In step S200, the radius of the optical zone in each direction is still 4.0 mm according to the field of view, but the defocus amount allocated in each direction is different.

[0168] Step S300: Define the nose side of the lens as 0°, the top of the lens as 90°, the temporal side as 180°, and the bottom of the lens as 270° to establish a coordinate system.

[0169] Step S400: Determine that the field of view below the lens (270°) achieves a 5.5D defocus at a radius of 3.0mm, and the defocus at a diameter of 3.0-4.0mm does not exceed 0.5D. Determine that the field of view above the lens (90°) achieves a 3.5D defocus at a radius of 3.0mm, and the defocus at a diameter of 3.0-4.0mm does not exceed 0.5D. Determine that the field of view on the nose side of the lens (0°) achieves a 3.5D defocus at a radius of 3.0mm, and the defocus at a diameter of 3.0-4.0mm does not exceed 0.5D. Determine that the field of view on the temporal side of the lens (180°) achieves a 6.5D defocus at a radius of 3.0mm, and the defocus at a diameter of 3.0-4.0mm does not exceed 0.5D. (The text repeats itself here.) Figure 11 As shown, based on the above content, it can be determined that... , , , Curves showing the change in optical power as a function of radius at four angles.

[0170] Step S500: Determine the curve of optical power as a function of angle on the semicircle corresponding to any radius r. The curve of optical power as a function of angle must satisfy the following formula (4).

[0171] (4)

[0172] Step S600, as follows Figure 12 and Figure 13 As shown, the circumferential optical power variation of an arbitrary radius envelope is continuous.

[0173] In this embodiment, the optical power at any point in the lens optics is greater than the optical power at the geometric center, or the optical power at some points in the optics is greater than the optical power at the geometric center, and the optical power at the remaining points is equal to the optical power at the geometric center. For example... Figure 14 As shown, Figure 14 The text lists several radii (0.5mm, 1.0mm, 1.5mm, 2.0mm, 2.5mm, 3.0mm, 3.5mm, 4.0mm) and shows that the circumferential optical power variation curves with angle are all continuously differentiable and conform to a sinusoidal function trend. For example... Figure 15 and Figure 16 As shown, Figure 15 and Figure 16 The curves showing the change in optical power with radius at several different angles (6°, 30°, 135°, 252°, 336°) are not entirely the same.

[0174] In this embodiment, the circular central region with a diameter of 1.8 mm is the central correction zone, and the annular region with a diameter of 1.8-8 mm is the defocus zone. The optical power at any angle in the defocus zone gradually increases with the radius, or the rate of change of optical power with the radius first increases and then decreases, and the rate of change is not zero. For example... Figure 17As shown, the rate of change of optical power with radius at several different angles has the same trend.

[0175] Example 3

[0176] In one specific embodiment of the present invention, the lens is a progressive focal length contact lens with a diameter of 14 mm. The lens is used for myopic patients to simultaneously slow the progression of myopia. The diameter of the optical part of the lens is 8.0 mm, and the vertex spherical power of the lens is 0.0D. The rear surface of the lens is spherical, and the front surface of the lens is aspherical. Figure 18 As shown, the lens in the prior art has a 360° rotationally symmetrical optical power distribution.

[0177] The following describes ophthalmic lens design methods in conjunction with the human eye's field of vision. These methods include:

[0178] In step S100, the upper field of view of the human eye is determined to be 50°, and the lower field of view of the human eye is determined to be 80° (occupying an angle range of 60°).

[0179] In step S200, the radius of the optical element in each direction is still 4.0mm according to the field of view. The defocus amount allocated in each direction is the same, but the trend of change in different directions is different, specifically, the size of the central flat area is different.

[0180] Step S300: Define the nose side of the lens as 0°, the top of the lens as 90°, the temporal side as 180°, and the bottom of the lens as 270° to establish a coordinate system.

[0181] Step S400: Determine that the field of view below the lens (270°) achieves a 5.0D defocus at a radius of 4.0mm, with a defocus of no more than 0.5D in diameter between 3.0 and 4.0mm, and a relatively flat central area approaching 0. This trend is the same within the lower 60° range (240°-300° range). Determine that the field of view above the lens (90°) achieves a 5.0D defocus at a radius of 4.0mm, with a defocus of no more than 0.5D in diameter between 3.0 and 4.0mm, and a relatively flat central area of ​​1.0mm. (The text repeats itself here.) Figure 19 As shown, it has been determined , Curves showing the change in optical power with radius at several different angles.

[0182] Step S500: Determine the curve of optical power as a function of angle on the semicircle corresponding to any radius r. The curve of optical power as a function of angle must satisfy the following formula (5). (5)

[0183] Step S600, as follows Figure 20 and Figure 21 As shown, the circumferential optical power variation of an arbitrary radius envelope is continuous.

[0184] In this embodiment, the optical power at any point in the lens optics is greater than the optical power at the geometric center, or the optical power at some points in the optics is greater than the optical power at the geometric center, and the optical power at the remaining points is equal to the optical power at the geometric center. For example... Figure 22 As shown, Figure 22 The text lists several curves showing the variation of circumferential optical power with angle for radii (0.5mm, 1.0mm, 1.5mm, 2.0mm, 2.5mm, 3.0mm, 3.5mm, 4.0mm), all of which are continuous, differentiable, and conform to a sinusoidal function trend. For example... Figure 23 and Figure 24 As shown, Figure 23 and Figure 24 The curves showing the change in optical power with radius at several different angles (6°, 30°, 135°, 252°, 336°) are not entirely the same.

[0185] Example 4

[0186] In one specific embodiment of the invention, the lens is an aphakic intraocular lens used to extend the depth of field. The diameter of the optical part is 5.0 mm, and the vertex spherical power of the lens is 26.0 D. The rear surface of the lens is spherical, and the front surface of the lens is aspherical. Figure 25 As shown, the lens in the prior art has a 360° rotationally symmetrical optical power distribution.

[0187] Step S200: Design the upper and lower parts of the lens to have a gradual focal length change, and design the nasal and temporal sides of the lens to have a refractive change, according to actual needs.

[0188] In step S300, a coordinate system is established by defining the nose side of the lens as 0°, the top of the lens as 90°, the temporal side of the lens as 180°, and the bottom of the lens as 270°.

[0189] Step S400: Determine that the upper (90°) and lower (270°) angles of the lens are both gradual focal length changes, while the nasal (0°) and temporal (180°) angles are both regional refraction changes. The determined curve shows the relationship between the lens radius and optical power. and like Figure 26 As shown.

[0190] Step S500: Determine the curve of optical power as a function of angle on the semicircle corresponding to any radius r. The curve must satisfy the following formula (6).

[0191] (6)

[0192] Where θ∈[0°,360°), r∈(0,2.5).

[0193] Step S600, as follows Figures 27 to 29 As shown, the circumferential optical power variation of an arbitrary radius envelope is continuous.

[0194] In this embodiment, the optical power of any point in the lens optics is greater than the optical power of the geometric center, or the optical power of some points in the optics is greater than the optical power of the geometric center, and the optical power of the remaining points is equal to the optical power of the geometric center. Figure 27 The figure lists several radii (0.5mm, 1.0mm, 1.5mm, 2.0mm, 2.5mm) and their corresponding circumferential optical power as a function of angle. All of these curves are continuously differentiable and conform to the trend of a sine function. Figure 28 and Figure 29 The curves showing the change in optical power with radius at several different angles (6°, 30°, 135°, 252°, 336°) are not entirely the same.

[0195] Example 5

[0196] In one specific embodiment of the present invention, the lens is a phakic intraocular lens used to alleviate eye strain to a certain extent. The diameter of the optical part is 5.6 mm, and the vertex spherical power of the lens is -10.0D. The rear surface of the lens is aspherical, and the front surface of the lens is aspherical. Figure 30 As shown, the lens in the prior art has a 360° rotationally symmetrical optical power distribution.

[0197] In step S300, a coordinate system is established by defining the nose side of the lens as 0°, the top of the lens as 90°, the temporal side of the lens as 180°, and the bottom of the lens as 270°.

[0198] Step S400: Design the lens as a graduated focal length (270°-360°) and as zero spherical aberration (60°-210°). Figure 31 As shown, Figure 31 An example is given showing the relationship between the radius of the lens and its optical power.

[0199] Step S500: Determine the curve of optical power versus angle on the semicircle corresponding to any radius r. The curve of angle variation must satisfy the following formula (7).

[0200] (7)

[0201] Step S600, as follows Figures 32 to 34 As shown, the circumferential optical power variation of an arbitrary radius envelope is continuous.

[0202] In this embodiment, the optical power at any point in the lens optics is greater than the optical power at the geometric center, or the optical power at some points in the optics is greater than the optical power at the geometric center, and the optical power at the remaining points is equal to the optical power at the geometric center. For example... Figure 32 As shown, Figure 32 The text lists several radii (0.5mm, 1.0mm, 1.5mm, 2.0mm, 2.5mm) and their corresponding circumferential optical power versus angle curves, all of which are continuously differentiable and conform to a sinusoidal function trend. For example... Figure 33 and Figure 24 As shown, Figure 33 and Figure 24 The curves showing the change in optical power with radius at several different angles (6°, 30°, 135°, 252°, 336°) are not entirely the same.

[0203] Example 6

[0204] It is not difficult to understand that the lenses described in Examples 1 to 5 are all equipped with Figure 9 The weighted structures and / or markings shown indicate that, for the convenience of lens positioning, the peripheral portion of the lens of the present invention has weighted structures (i.e., positioning structures) that are positioned circumferentially relative to the eyeball during wear or after implantation in the human eye. This embodiment provides various specific configurations of the weighted structures; some specific configurations of the positioning structures are described below.

[0205] like Figure 35 As shown, lens 8 has a thickened region 6 with increased thickness and a thinned region 7 with decreased thickness. The thickened region 6 and the thinned region 7 are positioned opposite each other across the center of lens 8 (180 degrees apart in the circumferential direction). The thickened region 6 and the thinned region 7 constitute a positioning structure that enables lens 8 to be positioned in the circumferential direction. Specifically, when the lens is worn, because the thickened region 6 is relatively heavier and the thinned region 7 is relatively lighter, lens 8 will rotate or remain in a circumferential position where the thickened region 6 is on the lower side and the thinned region 7 is on the upper side.

[0206] like Figure 36 As shown, the lens 8 has a weighted portion 3, which is fan-shaped and disposed in the peripheral region 2, located at the outer edge of the peripheral region 2. The weighted portion 3 can be formed by locally thickening the contact lens. In this embodiment, the width of the weighted portion 3 is the coverage area of ​​a 40° central angle.

[0207] In addition, the radial range of the fan-shaped weight portion 3 can be set to be within 7mm-15mm from the central correction zone, preferably 8mm-14mm or 9mm-13mm.

[0208] In addition, the area of ​​the weight-bearing part 3 can be set as follows: not limited to the above-mentioned 40°, the angle formed by the two sides of the weight-bearing part 3 in the circumferential direction is 10°-180°, preferably 20°-140° or 30°-110°.

[0209] like Figure 37 As shown, this embodiment is similar to... Figure 36 The main difference in the embodiment shown is that, in this embodiment, the width of the vertical weight 3 is the coverage area of ​​the 80° central angle.

[0210] like Figure 38 As shown, this embodiment is similar to... Figure 36 The main difference in the embodiment shown is that the width of the vertical weight 3 in this embodiment covers a central angle of 180°.

[0211] like Figure 39 As shown, this embodiment is similar to... Figure 36 The main difference in the illustrated embodiment is that the contact lens in this embodiment has two weight-bearing portions 3, which are arranged symmetrically and spaced apart in the circumferential direction. Of course, the number of weight-bearing portions 3 is not limited to this; more weight-bearing portions 3 can be provided. The structures of the multiple weight-bearing portions 3 can be the same or different. For example, three (an odd number) weight-bearing portions 3 can be provided, with the two weight-bearing portions 3 on both sides arranged symmetrically, and the middle weight-bearing portion 3 having a different structure (e.g., shape) than the weight-bearing portions 3 on both sides. Figure 40 As shown, this embodiment is similar to... Figure 39 The main difference in the illustrated embodiment is that, in this embodiment, the weight-bearing portion 3 is elliptical, with the long side of the ellipse extending circumferentially along the lens 8 and the short side extending approximately radially along the lens 8. As a variation, more elliptical weight-bearing portions 3 can be provided.

[0212] The range of the weight 3 in the radial direction of the contact mirror is set as follows: with several centers as the center, within the range of diameter 7mm-15mm, 8mm-14mm or 9mm-13mm.

[0213] The length (major axis) of the ellipse is 3-8 mm, preferably 3.5-7 mm or 4-6 mm. The width (minor axis) of the ellipse is 1-5 mm, preferably 1.5-4.5 mm or 2-4 mm. The distance between the multiple elliptical weight portions 3 and the outer edge of the contact lens is 0.01-0.3 mm, 0.03-0.2 mm or 0.05-0.15 mm.

[0214] like Figure 41 As shown, this embodiment is similar to... Figure 35 The main difference in the embodiments shown is that,

[0215] Both the thickening zone 6 and the thinning zone 7 are fan-shaped, and the width of both the thickening zone 6 and the thinning zone 7 (the range they occupy in the circumferential direction) is the range (area) covered by a central angle of 90°.

[0216] In this embodiment, the edge (peripheral area) of the contact lens is divided into four quadrants. The maximum thickness of the thickened area 6 is 0.2-0.7 mm, preferably 0.25-0.6 mm or 0.3-0.5 mm. The minimum thickness of the thinned area 7 is 0.05-0.4 mm, preferably 0.1-0.35 mm or 0.15-0.3 mm.

[0217] Of course, the division of the four quadrants is not limited to four equal parts (90 degrees). The setting range of the thickening zone 6 can also be 50°-130°, 65°-115°, or 80°-100°, and the setting range of the thinning zone 7 can also be 50°-130°, 65°-115°, or 80°-100°. The thickening zone 6 and the thinning zone 7 can be symmetrically distributed, or they can be asymmetrically distributed.

[0218] like Figures 42 to 44 As shown, the main difference between this embodiment and the above-described embodiment lies in the different formation method of the positioning structure. Specifically, in this embodiment, the thickness of the peripheral region 2 of the lens 8 increases from one end of a certain diameter (e.g., ...). Figure 42 The lower edge) crosses the center of the contact lens in the vertical direction towards the other end of the diameter (e.g. Figure 42 The upper edge gradually decreases in size.

[0219] like Figure 43 and Figure 44 As shown, the thickness T2 of the lens 8 at the lower edge of the peripheral region 2 is greater than the thickness T1 at the upper edge. Furthermore, the thickness distribution of the peripheral region 2 is relative to the diameter (e.g., ...). Figure 32 The diameters extending vertically are symmetrically distributed so that the thickness T3 on the left side is equal to the thickness T4 on the right side.

[0220] By making the thickness of the upper and lower edges of the lens 8 gradually transition, the thickness of the upper and lower edges of the lens 8 is not uniformly distributed, but presents a gradual trend. The thickness is the thickest part at the bottom of the lens 8, and it begins to thin out at a fixed ratio as it extends upwards, reaching the thinnest part at the top of the lens 8. The thickness is evenly distributed in the horizontal direction. The purpose is to make the weight-bearing part 3 gradually transition, so that while achieving weight positioning, the thickness of the lens 8 does not have a significant thickening area, thus improving comfort.

[0221] This arrangement divides the peripheral region 2 of lens 8 into two quadrants: the upper region is thinned, and the lower region is thickened. The maximum thickness of the thickened region 6 is 0.2-0.7 mm, 0.25-0.6 mm, or 0.3-0.5 mm. The minimum thickness of the thinned region 7 is 0.05-0.4 mm, 0.1-0.35 mm, or 0.15-0.3 mm.

[0222] like Figure 45As shown, the main difference between this embodiment and the above embodiment is that, in the above embodiment, the positioning structure includes two thinning regions 7, which are symmetrically arranged about the center of the lens 8. The lens 8 can be rotated to the correct position by the interaction between the eyelid and the eyeball. Specifically, because the eyelid exerts pressure on the eyeball, and the thickness of the lens 8 is uneven, the pressure from the eyelid automatically rotates the thicker edge to the area not covered by the eyelid, while the thinner edge rotates to the upper or lower position covered by the eyelid, thus positioning the lens 8.

[0223] In addition, in this embodiment, the width of the thinning region 7 is set as follows: the width L1 of the thinning region 7 in the chord direction is 8-14 mm, preferably 8.5-13 mm or 9-12 mm. The distance between two thinning regions 7 is 7.5-14 mm, preferably 8-12.5 mm or 8.5-11 mm.

[0224] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, and not to limit them; although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features; and these modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of the present invention.

Claims

1. An ophthalmic lens characterized by, The optical part of the lens has a geometric center, and the optical power at any point of the optical part satisfies one of the following conditions as the optical power at the geometric center: The optical power at any point of the optical unit is greater than the optical power at the geometric center; The optical power at any point of the optical unit is less than the optical power at the geometric center; The optical power at some points of the optical component is greater than the optical power at the geometric center, and the optical power at the remaining points is equal to the optical power at the geometric center. The optical power at some points of the optical component is less than the optical power at the geometric center, and the optical power at the remaining points is equal to the optical power at the geometric center. Within the optical section, the optical power is continuously distributed along the circumference of a circle with the geometric center as the center and any radius, and there are at least two angles where the optical power distribution along the radius has different trends.

2. The ophthalmic lens of claim 1, wherein, In the range of the optical portion with diameter D, the curve of the power of the circumference corresponding to any radius r changes with angle is continuously derivable, where θ ∈ [0°, 360°), r ∈ (0, D / 2].

3. The ophthalmic lens of claim 1, wherein, At least two angles θ1 and θ2 exist, the radial power curve corresponding to the angle θ1 changes with the radius The radial power curve corresponding to the angle θ2 changes with the radius are not the same, wherein θ1 ∈ [0°, 360°), θ2 ∈ [0°, 360°), r ∈ (0, D / 2].

4. The ophthalmic lens of claim 1, wherein, Within the scope of the optical portion, the power over the circumference corresponding to at least one radius r1 varies as a function of the angle is not constant, with θ ∈ [0°, 360°) and r1 ∈ (0, D / 2].

5. The ophthalmic lens of any of claims 1 to 4, wherein, A sector with one vertex coinciding with the geometric center, where the optical power varies with angle on any circle corresponding to r within the sector, follows the trend of a sine function.

6. The ophthalmic lens of any of claims 1 to 4, wherein, Within the scope of the optical section, on at least one diameter passing through the geometric center, the optical power distribution trends of the two radii are not the same; on the remaining diameters passing through the geometric center, the optical power distribution trends of the two radii are symmetrical about the geometric center, that is: , r∈(0, D / 2], θ∈[0°, 180°), and θ is not equal to the direction of the diameter where the optical power distribution trend is different.

7. The ophthalmic lens of any of claims 1 to 4, wherein, In the semicircle range formed by 0°-180°, the power of light at any angle θ1 and θ2 varies with the radius, that is Where θ∈(0°, 180°), r∈(0, D / 2].

8. The ophthalmic lens of claim 7, wherein, The trend of the power of the light on the semicircle corresponding to any radius r changes with the angle, which conforms to wherein θ ∈ (0°, 180°), r ∈ (0, D / 2], and a and b are constants.

9. The ophthalmic lens of claim 7, wherein, The curve of optical power on a semicircle with arbitrary radius r as a function of angle conforms to the following formula (1); （1） where r e (0, D / 2], , is a constant, .

10. The ophthalmic lens of claim 7, wherein, The trend of optical power on a semicircle with any radius r as a function of angle conforms to the following formula (2); （2） where r e (0, D / 2], , is a constant, .

11. The ophthalmic lens of any of claims 1 to 4, wherein, The power of the light in the radial direction as a function of the radius for an arbitrary angle θ Continuous derivable, where θ ∈ [0°, 360°) and r ∈ (0, D / 2].

12. The ophthalmic lens of any of claims 1-4, wherein, The lens includes a contact lens, which is a corneal contact lens or a scleral contact lens, and the diameter of the optical part of the corneal contact lens and the optical part of the scleral contact lens are both 6-12mm.

13. The ophthalmic lens according to any one of claims 1 to 4, characterized in that, The lens includes an intraocular phakic intraocular lens, and the diameter of the optical part of the intraocular phakic intraocular lens is 4-8 mm.

14. The ophthalmic lens of claim 12, wherein, The lens is a progressive focal length contact lens used for myopic patients to simultaneously slow down the progression of myopia. The rear surface of the lens is spherical, and the front surface of the lens is aspherical.

15. The ophthalmic lens of claim 12, wherein, The lens is a phakic intraocular lens used to alleviate eye strain to a certain extent. The rear surface of the lens is aspherical, and its front surface is aspherical.

16. The ophthalmic lens of claim 12, wherein, The lens is an aphakic intraocular lens used to extend the depth of field. The rear surface of the lens is spherical, and the front surface of the lens is aspherical.

17. The ophthalmic lens of any one of claims 1 to 4, wherein, The lens includes an aphakic intraocular lens, and the diameter of the optical part of the aphakic intraocular lens is 4-8 mm.

18. The ophthalmic lens of claim 14, wherein, The optical part of the contact lens includes a central correction zone centered on the geometric center and a defocus zone surrounding the central correction zone. The optical power at any point within the central correction zone is equal, and the optical power of the defocus zone is greater than or equal to the optical power of the central correction zone. Furthermore, the optical power distribution trend along the radius of the defocus zone differs at at least two angles.

19. The ophthalmic lens of claim 18, wherein, The diameter of the optical part of the contact lens is 6-12mm, and the diameter of the central correction zone is 1-3.5mm.

20. The ophthalmic lens of claim 18, wherein, The curve of optical power changing with radius at any angle within the defocus zone is continuously differentiable.

21. The ophthalmic lens of claim 18, wherein, The defocused region has a non-continuous optical power variation curve with radius at at least one angle.

22. The ophthalmic lens of claim 18, wherein, The optical power at any angle in the defocused area gradually increases with the radius, or the rate of change of the optical power at any angle in the defocused area with the radius is continuous and first increases and then decreases, and the rate of change is not 0.

23. The ophthalmic lens according to claim 22, characterized in that, The rate of change of optical power with radius at any angle in the defocused region is uniform.

24. The ophthalmic lens of claim 18, wherein, The defocused region has at least one angle where the rate of change of optical power with radius is discontinuous.

25. The ophthalmic lens of claim 12, wherein, The lens has a positioning structure that positions it circumferentially relative to the eyeball when worn or after implantation in the human eye.

26. The ophthalmic lens of claim 25, wherein, The positioning structure includes a weighted part, which is disposed in the peripheral area around the optical area, and the weighted parts of the multiple lenses have different relative positions in the circumferential direction.

27. The ophthalmic lens of claim 26, wherein, The weight-bearing portion is formed by providing a thickened area in the surrounding region.

28. The ophthalmic lens of claim 26, wherein, The weight-bearing part is disposed on the edge of the lens. There are one or more weight-bearing parts, and multiple weight-bearing parts are symmetrically arranged. The shape of the weight-bearing part is fan-shaped, ring-shaped, crescent-shaped, circular, or flat-circular.

29. The ophthalmic lens of claim 26, wherein, The weight-bearing part extends circumferentially, and its circumferential range is 10°-180°, 20°-140°, or 30°-110°.

30. The ophthalmic lens of claim 26, wherein, The major axis of the plurality of elliptical vertical weights extends circumferentially along the lens, and the minor axis extends radially along the lens.

31. The ophthalmic lens of claim 25, wherein, The positioning structure includes a thickened area and a thinned area, which are located on the same diameter of the contact lens and are positioned opposite each other on both sides of the center of the contact lens.

32. The ophthalmic lens of claim 31, wherein, The thickened area has a circumferential range of 50°-130°, 65°-115°, or 80°-100°.

33. The ophthalmic lens of claim 31, wherein, The thinning zone has a circumferential range of 50°-130°, 65°-115°, or 80°-100°.

34. The ophthalmic lens of claim 31, wherein, The thickened region and the thinned region are asymmetrically distributed.

35. The ophthalmic lens of claim 26, wherein, The thickness of the peripheral area gradually decreases along the length of one diameter of the contact mirror, thereby forming the positioning structure.

36. The ophthalmic lens of claim 25, wherein, The positioning structure includes at least two thinning regions, which are located on the same diameter of the contact lens and are arranged opposite to each other on both sides of the center of the contact lens.

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