CN117572662A - Optical lens for eye vision and glasses - Google Patents
Optical lens for eye vision and glasses Download PDFInfo
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- CN117572662A CN117572662A CN202311375940.4A CN202311375940A CN117572662A CN 117572662 A CN117572662 A CN 117572662A CN 202311375940 A CN202311375940 A CN 202311375940A CN 117572662 A CN117572662 A CN 117572662A
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- 230000003287 optical effect Effects 0.000 title claims abstract description 105
- 239000011521 glass Substances 0.000 title abstract description 11
- 230000004438 eyesight Effects 0.000 title abstract description 8
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- 230000002093 peripheral effect Effects 0.000 claims abstract description 14
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- 239000002356 single layer Substances 0.000 claims description 8
- 238000000034 method Methods 0.000 claims description 2
- 230000000007 visual effect Effects 0.000 abstract description 15
- 210000000608 photoreceptor cell Anatomy 0.000 abstract description 11
- 210000001508 eye Anatomy 0.000 abstract description 7
- 210000004027 cell Anatomy 0.000 description 14
- 210000001525 retina Anatomy 0.000 description 10
- 238000012937 correction Methods 0.000 description 8
- 208000001491 myopia Diseases 0.000 description 8
- 230000000694 effects Effects 0.000 description 7
- 230000004379 myopia Effects 0.000 description 7
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- 230000004423 myopia development Effects 0.000 description 4
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- 229920003229 poly(methyl methacrylate) Polymers 0.000 description 3
- 229920000139 polyethylene terephthalate Polymers 0.000 description 3
- 239000005020 polyethylene terephthalate Substances 0.000 description 3
- 239000004926 polymethyl methacrylate Substances 0.000 description 3
- 230000002207 retinal effect Effects 0.000 description 3
- 238000010586 diagram Methods 0.000 description 2
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- 239000004417 polycarbonate Substances 0.000 description 2
- 229920000515 polycarbonate Polymers 0.000 description 2
- -1 polyethylene terephthalate Polymers 0.000 description 2
- 230000002265 prevention Effects 0.000 description 2
- 230000006978 adaptation Effects 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000004456 color vision Effects 0.000 description 1
- 230000008094 contradictory effect Effects 0.000 description 1
- 230000003111 delayed effect Effects 0.000 description 1
- 230000006870 function Effects 0.000 description 1
- 210000003128 head Anatomy 0.000 description 1
- 238000003384 imaging method Methods 0.000 description 1
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- 230000004048 modification Effects 0.000 description 1
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Classifications
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- G—PHYSICS
- G02—OPTICS
- G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
- G02C7/00—Optical parts
- G02C7/02—Lenses; Lens systems ; Methods of designing lenses
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- G—PHYSICS
- G02—OPTICS
- G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
- G02C7/00—Optical parts
- G02C7/02—Lenses; Lens systems ; Methods of designing lenses
- G02C7/06—Lenses; Lens systems ; Methods of designing lenses bifocal; multifocal ; progressive
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- Health & Medical Sciences (AREA)
- Ophthalmology & Optometry (AREA)
- Physics & Mathematics (AREA)
- General Health & Medical Sciences (AREA)
- General Physics & Mathematics (AREA)
- Optics & Photonics (AREA)
- Eyeglasses (AREA)
Abstract
The invention discloses an eye vision optical lens, which is provided with: a central optical zone; and a plurality of peripheral defocus regions, each defocus region having a plurality of microlenses, the micro lens of each defocusing area is surrounded to be annular and surrounds the central optical area, and a plurality of defocusing areas are sequentially arranged at intervals along the radial direction of the central optical area; the center of each defocusing area and the pupil center of the eyeball form an angle of view, and the included angle between the angles of view corresponding to the centers of every two adjacent defocusing areas is 2 times of a preset angle. The invention discloses an ophthalmic optical lens which can solve the problem that when the angle of view is gradually increased, the number of photoreceptor cells corresponding to the eyeball area is gradually reduced, and the high-density defocusing microlenses of the existing defocusing lens distributed at equal intervals generate redundant defocusing signals in the eyeball area, so that the visual effect is blurred. In addition, the invention also discloses glasses.
Description
Technical Field
The invention relates to the technical field of eye vision optics, in particular to an eye vision optical lens and glasses.
Background
Peripheral hyperopic defocus of the retina means that an object image at the central vision of a normal single-vision lens can be clearly projected onto the retina, but its periphery is projected behind the retina. Peripheral hyperopic defocus of the retina induces self-accommodation of the retinal back growth, which leads to a further increase in the length of the eye axis, which leads to a deepening of the myopic degree. The existing myopia prevention and control technology is based on the peripheral defocus theory, and can prevent the axial backward growth of eyes and delay the deepening of myopia by correcting the peripheral hyperopic defocus of retina.
At present, the lens of the glasses is usually specially designed, and the far vision around the retina is pulled back to the front of the retina in a mode of increasing diopter at the periphery of the lens, so that the deepening of myopia is controlled. However, the increasing rule of the peripheral diopter of the existing defocusing lens does not accord with the distribution rule of fundus photoreceptor cells, so that the effect of controlling myopia by peripheral defocusing is poor.
Disclosure of Invention
The invention mainly aims to provide an ophthalmic optical lens and glasses, and aims to solve the problems that when the angle of view is gradually increased, the number of photoreceptor cells corresponding to an eyeball area is gradually reduced, and redundant defocus signals are generated in the eyeball area by high-density defocus microlenses of the existing defocus lenses distributed at equal intervals, so that the visual effect is blurred.
To achieve the above object, the present invention provides an ophthalmic optical lens provided with:
a central optical zone; and
the lens system comprises a plurality of peripheral defocusing areas, a plurality of lens units and a lens unit, wherein each defocusing area is provided with a plurality of micro lenses, the micro lenses of each defocusing area are arranged in a surrounding mode and surround the central optical area, and the plurality of defocusing areas are sequentially arranged at intervals along the radial direction of the central optical area;
the center of each defocusing area and the pupil center of the eyeball can form an angle of view, and the included angle between the corresponding angles of view of the centers of every two adjacent defocusing areas is 2 times of a preset angle.
Preferably, the preset angle is expressed as:wherein Δθ represents the preset angle; r is (r) 1 Representing the radius corresponding to the inner ring of the first defocus region, r 2 Representing a radius corresponding to an outer ring of a first defocus region, the first defocus region being a defocus region having a minimum distance from the central optical zone; d represents the ophthalmic optical lens and the pupilDistance between hearts.
Preferably, the spacing between each two adjacent defocus regions increases radially outwardly of the central optic zone.
Preferably, the spacing between every two adjacent defocus regions satisfies: Δr n ＝dtan(θ n +2Δθ)-dtan(θ n ) The method comprises the steps of carrying out a first treatment on the surface of the Wherein n represents an nth defocus region disposed radially along the central optical zone; Δr n Representing the spacing between the nth defocus region and the n+1th defocus region; θ n Representing a central angle formed by the central line of the nth defocusing area and the pupil center, wherein the central line of the defocusing area is a line with equal distance to the inner ring of the defocusing area and the outer ring of the defocusing area respectively; Δθ represents the preset angle.
Preferably, the inner ring of each defocus region and the pupil center form a first field angle, the outer ring of each defocus region and the pupil center form a second field angle, and the difference between the second field angle and the first field angle is the preset angle.
Preferably, the defocus amount of the defocus region ranges from +2d to +5d.
Preferably, a single-layer annular microlens is arranged in the defocusing region, and the annular width of the defocusing region is equal to the diameter of the corresponding microlens; or, a plurality of layers of annular microlenses are arranged in the defocusing area, and the annular width of the defocusing area is larger than the diameter of the corresponding microlens.
Preferably, a plurality of microlenses of each of said defocus regions are arranged in spaced or contacting relation; the diameter of the micro lens ranges from 0.5 mm to 1.2mm.
Preferably, the ophthalmic optical lens comprises a lens body, the central optical zone and the defocus zone are arranged on the lens body, and the lens body and the micro lens are integrally formed.
The invention further proposes an eyeglass comprising a frame and an ophthalmic optical lens as described above, the ophthalmic optical lens being fixed to the frame.
The technical scheme of the invention is as follows: the ocular optical lens is used as a multi-point defocusing lens, a plurality of defocusing areas are distributed according to the angle of view to form concentric rings with increased intervals, when the angle of view is gradually increased, the number of photoreceptor cells corresponding to the eyeball area is gradually reduced, the interval between the defocusing areas is gradually increased, so that the density of the micro lenses is gradually reduced, the incident light can be imaged at the position in front of the retina of the eyeball, the visual quality and visual effect of the ocular optical lens can be effectively improved, the ocular optical lens has the effect of delaying myopia development, and the myopia control effect of the ocular optical lens is improved.
Drawings
Fig. 1 is a schematic view of an ophthalmic optical lens according to an embodiment of the present invention.
Fig. 2 is a schematic view of the field angle of the defocus region of the ophthalmic optical lens shown in fig. 1.
FIG. 3 is a graph showing the relationship between the number of photoreceptor cells and the angle from the fovea according to the embodiment of the present invention.
FIG. 4 is a chart showing the photoreceptor cell characteristics according to an embodiment of the present invention.
Fig. 5 is a schematic diagram of glasses according to an embodiment of the present invention.
The achievement of the objects, functional features and advantages of the present invention will be further described with reference to the accompanying drawings, in conjunction with the embodiments.
Detailed Description
The following description of the embodiments of the present invention will be made more clearly and fully with reference to the accompanying drawings, in which it is evident that the embodiments described are only some, but not all embodiments of the invention. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
It should be noted that all directional indicators (such as up, down, left, right, front, and rear … …) in the embodiments of the present invention are merely used to explain the relative positional relationship, movement, etc. between the components in a particular posture (as shown in the drawings), and if the particular posture is changed, the directional indicator is changed accordingly.
It will also be understood that when an element is referred to as being "mounted" or "disposed" on another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present.
Furthermore, the description of "first," "second," etc. in this disclosure is for descriptive purposes only and is not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include at least one such feature. In addition, the technical solutions of the embodiments may be combined with each other, but it is necessary to base that the technical solutions can be realized by those skilled in the art, and when the technical solutions are contradictory or cannot be realized, the combination of the technical solutions should be considered to be absent and not within the scope of protection claimed in the present invention.
Referring to fig. 1 and fig. 2 in combination, fig. 1 is a schematic view of an ophthalmic optical lens according to an embodiment of the present invention, and fig. 2 is a schematic view of an angle of field of an out-of-focus area of the ophthalmic optical lens according to an embodiment of the present invention. The ocular optical lens 1 is a near-sighted lens, and can be applied to glasses, vision correction devices, and the like for improving visual experience and correcting visual effects. The ocular optical lens 1 is provided with a central optical zone S0 and a plurality of peripheral defocus zones S1, each defocus zone S1 is provided with a plurality of microlenses 20, and the microlenses 20 of each defocus zone S1 are annularly surrounded by the central optical zone S0. The plurality of defocus regions S1 are sequentially arranged at intervals in the radial direction of the central optical region S0. The center of each defocus region S1 can form an angle of view θ with the pupil center O of the eyeball, and the included angle between the angles of view θ corresponding to the centers of every two adjacent defocus regions S1 is 2 times the preset angle.
In this embodiment, the ophthalmic optical lens 1 is divided into a central optical zone S0 and a plurality of defocus zones S1, the ophthalmic optical lens 1 includes a plurality of microlenses 20, and all the microlenses 20 are disposed on the same side of the ophthalmic optical lens 1. Each of the defocus regions S1 is provided with a plurality of microlenses 20, the microlenses 20 of each of the defocus regions S1 are surrounded to form a ring shape, and all the microlenses 20 are disposed around the central optical region S0. Specifically, the central optical zone S0 is circular, and all the defocus zones S1 are annular. The plurality of defocusing areas S1 are sequentially arranged at intervals along the radial direction X of the central optical area S0, and the circle centers of all the defocusing areas S1 are coincident with the circle center of the central optical area S0. It will be appreciated that the diameter of the defocus region S1 increases in sequence along the radial direction X of the central optic region S0.
In this embodiment, when the ocularly optical lens 1 is worn on the head of a human body, the center of each defocus region S1 and the pupil center O form a field angle θ, and the included angle between the center of each two adjacent defocus regions S1 and the corresponding field angle θ is set to be 2 times of a predetermined angle. That is, the included angle between the angles of view θ of any two adjacent defocus regions S1 is a preset angle of 2 times.
The ocular optical lens 1 is used as a multi-point defocusing lens, a plurality of defocusing areas S1 are distributed according to the angle of view, all the defocusing areas S1 form concentric rings with increased intervals, when the angle of view theta is gradually increased, the number of photoreceptor cells corresponding to the eyeball area is gradually reduced, the interval between the defocusing areas S1 is gradually increased, so that the number of microlenses 20 in unit area of the lens is gradually reduced, the fewer density microlenses 20 can enable incident light rays to be imaged at the position in front of the retina of the eyeball, and can also avoid generating excessive defocusing signals, effectively improve the visual quality and visual effect of the ocular optical lens 1, simultaneously meet the requirement that the ocular optical lens 1 has the effect of delaying myopia development, and improve the effect of controlling myopia by the ocular optical lens 1.
In some embodiments, the preset angle is expressed as:wherein Δθ represents a preset angle; r is (r) 1 Representing the radius corresponding to the inner ring of the first defocus region, r 2 Representing a radius corresponding to an outer ring of a first defocus region, the first defocus region being a defocus region S1 having a minimum distance from the central optical zone S0; d represents the distance between the ocular optical lens 1 and the pupil center O.
In this embodiment, the center of each defocus region S1 forms a central line with the pupil center O. The included angle between the field angles theta corresponding to the centers of any two adjacent defocused areas S1 is the included angle between the central connecting lines of the two adjacent defocused areas S1. The included angle between the angles of view theta corresponding to the centers of any two adjacent defocused areas S1 is 2delta theta. The distance between the ocular optical lens 1 and the pupil center O is the distance between the center of the surface of the ocular optical lens 1 near the eyeball and the pupil center O. The distance between the center of the ocular optical lens 1 and the pupil center O is usually 12 to 13mm. It will be appreciated that the predetermined angle Δθ is determined by the size of the first defocus region, and is a fixed value when both the inner diameter and the outer diameter of the first defocus region are determined. It will be appreciated that the angles of view θ at any corresponding position of any adjacent two defocus regions S1 are all the same. Wherein the first defocus region is the defocus region S1 closest to the center P of the central optical region S0.
In some embodiments, the spacing between each two adjacent defocus regions S1 increases outwardly in the radial direction X of the central optic region S0.
In this embodiment, any point on the inner ring of the defocus region S1 forms a first connection line with the pupil center O, and any point on the outer ring of the defocus region S1 forms a second connection line with the pupil center O; the center P of the central optical zone S0 forms a third line (i.e., the optical axis of the ophthalmic optical lens 1) with the pupil center O. Since the included angle θ between any two adjacent defocus regions S1 is set to 2Δθ, the included angle formed between the first, second and third lines of the defocus region S1 is larger and larger along the radial direction X of the central optical region S0, i.e., the larger the field angle of the defocus region S1, the larger the distance between every two adjacent defocus regions S1. Accordingly, the number of microlenses 20 per unit area of the ocular optical lens 1 gradually decreases outward in the radial direction X of the central optical zone S0, and the lesser density of microlenses 20 enables incident light to be imaged at a position in front of the retina of the eyeball while avoiding the generation of excessive defocus signals to cause visual blur.
In some embodiments, the spacing between each two adjacent defocus regions S1 satisfies: Δr n ＝dtan(θ n +2Δθ)-dtan(θ n ). Wherein n represents the radial direction along the central optical zoneAn nth defocus region of X; Δr n Representing the spacing between the nth defocus region and the n+1th defocus region; θ n The center angle formed by the center line L of the nth defocusing area and the pupil center O is shown, and the center line L of the defocusing area S1 is a line with equal distances from the inner ring of the defocusing area S1 and the outer ring of the defocusing area S1 respectively; Δθ represents a preset angle.
In this embodiment, the center lines L of the defocus regions S1 are all circular, and the distance between the center line L and the corresponding inner ring is equal to the distance between the corresponding outer ring. The distance between two adjacent defocus regions S1 is the distance between the centerlines L of the two adjacent defocus regions S1. The radius of the center line L of the defocus region S1 can be expressed as: r is (r) n+1 ＝r n +Δr n . Wherein r is n+1 A radius representing the centerline L of the n+1th defocus region; r is (r) n Representing the radius of the centerline L of the nth defocus region. It will be appreciated that when both the inner and outer diameters of the first defocus region are determined, the size of the remaining defocus region S1 can be determined accordingly.
According to the existing medical research results, the number of photoreceptor cells per square millimeter of the fundus gradually decreases with increasing angle from the fovea. As the angle of view increases gradually, the number of photoreceptor cells in the area where the non-normal light acts decreases gradually. Considering the sparse distribution of the retinal peripheral rod cells, the interval between each ring of defocus regions S1 is correspondingly increased according to the equal (2delta#) of the angle of view, the interval between defocus regions S1 is increased according to the angle of view, and the number of microlenses 20 in unit area on the lens can be gradually reduced along the radial outward direction of the center of the lens, so that the defocused lens is designed, the distribution rule of fundus photoreceptor cells is more met, the effect of delaying myopia development is ensured, the visual quality of the ocular optical lens 1 is improved, and more comfortable wearing experience is provided for a wearer.
In some embodiments, the inner ring of each defocus region S1 forms a first angle of view with the pupil center O, the outer ring of each defocus region S1 forms a second angle of view with the pupil center O, and the difference between the second angle of view and the first angle of view is a preset angle Δθ.
In this embodiment, a first angle of view is formed between the first line and the third line of the defocus region S1, a second angle of view is formed between the second line and the third line of the defocus region S1, and the increment of the angle of view θ of the defocus region S1 is an included angle formed between the corresponding first line and second line.
In this embodiment, the included angle between the angles of view of two adjacent defocus regions S1 is 2 times the preset angle, and the difference between the first angle of view and the second angle of view of each defocus region S1 is also the preset angle, and it can be understood that the width variation of the defocus region S1 and the distance variation of two adjacent defocus regions S1 are equal angles of view. For example, if the preset angle is 2 °, the field angle corresponding to the edge of the central optical zone S0 is set to 2 °, the field angle corresponding to the field angle between 2 ° and 4 ° is the first defocus region, the field angle corresponding to the field angle between 4 ° and 6 ° is the interval region between the first defocus region and the second defocus region, the field angle corresponding to the field angle between 6 ° and 8 ° is the second defocus region, the field angle corresponding to the field angle between 8 ° and 10 ° is the interval region between the second defocus region and the third defocus region, and so on.
In some embodiments, the defocus amount of defocus region S1 ranges from +2d to +5d.
In this embodiment, the defocus amount of the microlens 20 in the defocus region S1 is set between +2d to +5d, so that the ocular optical lens 1 has a better myopia prevention and control effect, and the ocular optical lens 1 has better visual quality.
In some embodiments, a single layer of annular microlenses 20 are disposed within the defocus region S1, with the annular width of the defocus region S1 being equal to the diameter of the corresponding microlens 20. Alternatively, a plurality of layers of annular microlenses 20 are disposed in the defocus region S1, and the annular width of the defocus region S1 is larger than the diameter of the corresponding microlens 20.
In this embodiment, a single-layer annular microlens 20 may be provided in the defocus region S1, or a multi-layer annular microlens 20 may be provided. When a single-layer annular microlens 20 is disposed in the defocus region S1, the annular width of the defocus region S1 is equal to the diameter of the corresponding microlens 20. When the multi-layered annular microlenses 20 are disposed within the defocus region S1, the annular width of the defocus region S1 is larger than the diameter of the corresponding microlens 20.
Specifically, the defocus region S1 adjacent to the central optical region S0 is a first defocus region, the first defocus region is provided with a single-layer annular microlens 20, the connection lines of the inner edges of all microlenses 20 form an inner ring of the first defocus region, the connection lines of the outer edges of all microlenses 20 form an outer ring of the first defocus region, and the inner ring and the outer ring together form an annular first defocus region. Thus, the annular width of the first defocus region is the same as the diameter of the microlens 20.
Each of the other defocus regions S1 except the first defocus region is provided with at least one layer of annular microlenses 20. When the defocusing area S1 comprises a single-layer annular micro lens 20, the diameter of the micro lens 20 is smaller than or equal to the annular width of the defocusing area S1, and the circle centers of the micro lenses 20 are all positioned on the central line L of the corresponding defocusing area S1; when the defocus region S1 includes two layers of annular microlenses 20, the sum of the diameters of the two layers of microlenses 20 is less than or equal to the annular width of the defocus region S1, and the center point between the two layers of microlenses 20 is located on the center line L of the corresponding defocus region S1. For example, when the annular width of the defocus region S1 is 2mm, and the defocus region S1 is provided with a single layer of microlenses 20, the diameter of the microlenses 20 is less than or equal to 2mm. When the annular width of the defocus region S1 is 2mm and the defocus region S1 is provided with two layers of microlenses 20, the diameter of the microlenses 20 may be 1mm and the two layers of microlenses 20 are arranged tangentially.
In some embodiments, the plurality of microlenses 20 of each defocus region S1 are disposed in spaced or contacting relation. The diameter of the microlens 20 ranges from 0.5 to 1.2mm.
In this embodiment, the microlenses 20 of each defocus region S1 are disposed in contact, or the microlenses 20 of each defocus region S1 are disposed at intervals and uniformly distributed. When the microlenses 20 of the defocus region S1 are arranged at intervals, the pitches between all the microlenses 20 in the same defocus region S1 are the same. When the microlenses 20 of the defocus region S1 are disposed in contact, the microlenses 20 are abutted against each other or partially overlapped with each other. The shape of the microlens 20 may be circular arc, polygonal, etc., and is not limited herein.
In this embodiment, the diameter of the microlens 20 of each defocus region S1 is smaller than or equal to the annular width of the corresponding defocus region S1. In the case where the ocular optical lenses 1 are the same in size, the number of defocus regions S1 is determined by the diameter of the microlens 20.
Taking the ophthalmic optical lens 1 shown in fig. 1 as an example, the micro lenses 20 each have a diameter of 1.0mm, and the ophthalmic optical lens 1 includes 8 defocus regions S1. When the radius of the first defocus region is 4.60mm, the radius of the second defocus region is 6.76mm, the radius of the third defocus region is 9.25mm, the radius of the fourth defocus region is 11.91mm, the radius of the fifth defocus region is 14.78mm, the radius of the sixth defocus region is 17.96mm, the radius of the seventh defocus region is 21.54mm, and the radius of the eighth defocus region is 25.68mm.
In some embodiments, the ophthalmic optical lens 1 includes a lens body 10, a central optical zone S0 and a defocus zone S1 are provided on the lens body 10, and the lens body 10 is integrally formed with the microlens 20.
In the present embodiment, the ocular optical lens 1 includes a lens body 10 and microlenses 20, the lens body 10 forming a central optical zone S0 and a defocus zone S1. The central optical zone S0 is located at the center of the lens body 10, an annular correction zone S2 is formed between two adjacent defocus zones S1, and a plurality of defocus zones S1 and a plurality of annular correction zones S2 are alternately disposed outside the central optical zone S0. It can be understood that the lens body 10 is a correction zone as a whole, the first defocus region surrounds the central optical zone S0, and an annular correction zone S2 is disposed between every two adjacent defocus regions S1. Correspondingly, the annular correction areas S2 are all annular. The central optical zone S0 is located at the center of the lens body 10, and the centers of all annular correction zones S2, the centers of all defocus zones S1, and the center of the central optical zone S0 are all coincident.
The central optical zone S0 and the peripheral annular correction zones S2 are each used for correcting the refractive power of the refractive error of the eye. The annular defocusing areas S1 and the annular correcting areas S2 are alternately arranged, and the distance between two adjacent annular defocusing areas S1 is changed at equal angles, so that the stability of peripheral vision imaging of the ocular optical lens 1 can be ensured while the ocular optical lens 1 has a defocusing function.
As shown in fig. 3, cone cells are most densely distributed in the fovea area, and there is almost no cone cell distribution in the area outside the fovea; the rods are most densely distributed in the range of 15-25 degrees from the fovea, and sparsely distributed at the retinal edge. From a photoreceptor cell characteristic comparison table (shown in fig. 4), it is known that cone cells are mainly responsible for color perception, and rod cells are mainly responsible for light-sensitive perception. It is available in combination with the peripheral defocus theory that peripheral defocus signals act mainly on rod cells.
According to the change of the distribution density curves of the cone cells and the rod cells, the intersection point of the cone cells and the rod cells can be taken as the reference of the radius of the central optical zone S0, so that the influence of the micro lens 20 on the cone cells for sensing the color is reduced, the visual quality of the central visual field is ensured, the defocusing signal is ensured to be precisely acted on most rod cells, and the myopia development is delayed. In this embodiment, according to the intersection point of the cone-shaped visual cell and the rod-shaped visual cell distribution density curve, the radius of the first defocus region is calculated to be 4.60mm, that is, the distance between the center line L of the first defocus region and the center of the central optical zone S0 is calculated to be 4.6mm.
In this embodiment, the lens body 10 and the microlenses 20 of all the defocus regions S1 are integrally molded by injection molding. Wherein the lens body 10 may be a thermoplastic lens, such as a PC lens. The microlens 20 may be made of one of polymethyl methacrylate (polymethyl methacrylate, PMMA), polyethylene terephthalate (Polyethylene terephthalate, PET), or Polycarbonate (PC).
Please refer to fig. 5 in combination, which is a schematic diagram of glasses according to an embodiment of the present invention. The glasses 2 include a frame 3 and an eyepiece optical lens 1, and the eyepiece optical lens 1 is fixed to the frame 3.
The specific structure of the ocular optical lens 1 refers to the above-described embodiment. The glasses 2 adopt all the technical solutions of all the embodiments, so at least have all the beneficial effects brought by the technical solutions of the embodiments, and are not described in detail herein.
The above description of the preferred embodiments of the present invention should not be taken as limiting the scope of the invention, but rather should be understood to cover all modifications, variations and adaptations of the present invention using its general principles and the following detailed description and the accompanying drawings, or the direct/indirect application of the present invention to other relevant arts and technologies.
Claims (10)
1. An ophthalmic optical lens, characterized in that the ophthalmic optical lens is provided with:
a central optical zone; and
the lens system comprises a plurality of peripheral defocusing areas, a plurality of lens units and a lens unit, wherein each defocusing area is provided with a plurality of micro lenses, the micro lenses of each defocusing area are arranged in a surrounding mode and surround the central optical area, and the plurality of defocusing areas are sequentially arranged at intervals along the radial direction of the central optical area;
the center of each defocusing area and the pupil center of the eyeball can form an angle of view, and the included angle between the angles of view corresponding to the centers of every two adjacent defocusing areas is 2 times of a preset angle.
2. The ophthalmic optical lens of claim 1 wherein the predetermined angle is expressed as:wherein Δθ represents the preset angle; r is (r) 1 Representing the radius corresponding to the inner ring of the first defocus region, r 2 Representing a radius corresponding to an outer ring of a first defocus region, the first defocus region being a defocus region having a minimum distance from the central optical zone; d represents the distance between the ocular optical lens and the pupil center.
3. The ophthalmic optical lens of claim 1 wherein the spacing between each two adjacent defocus regions increases radially outward of the central optical zone.
4. A spectacle optical lens as claimed in claim 3, wherein the spacing between each two adjacent defocus regions is such that: Δr n ＝dtan(θ n +2Δθ)-dtan(θ n ) The method comprises the steps of carrying out a first treatment on the surface of the Wherein n represents an nth defocus region disposed radially along the central optical zone; Δr n Representing the spacing between the nth defocus region and the n+1th defocus region; θ n Represents the center angle formed by the center line of the nth defocus region and the pupil center,the center line of the defocusing area is a line with equal distance to the inner ring of the defocusing area and the outer ring of the defocusing area respectively; Δθ represents the preset angle.
5. The ophthalmic optical lens of claim 1 wherein the inner ring of each of the defocus regions forms a first angle of view with the pupil center and the outer ring of each of the defocus regions forms a second angle of view with the pupil center, the difference between the second angle of view and the first angle of view being the predetermined angle.
6. The ophthalmic optical lens of claim 1 wherein the defocus amount of the defocus region ranges from +2d to +5d.
7. The ophthalmic optical lens of claim 1 wherein a single layer of annular microlenses is disposed within the defocus region, the annular width of the defocus region being equal to the diameter of the corresponding microlens; or, a plurality of layers of annular microlenses are arranged in the defocusing area, and the annular width of the defocusing area is larger than the diameter of the corresponding microlens.
8. The ophthalmic optical lens of claim 7 wherein a plurality of microlenses of each of the defocus regions are disposed in spaced or contacting relation; the diameter of the micro lens ranges from 0.5 mm to 1.2mm.
9. The ophthalmic optical lens of claim 1 wherein the ophthalmic optical lens comprises a lens body, the central optical zone and the defocus zone being provided in the lens body, the lens body being integrally formed with the microlenses.
10. An eyeglass comprising a frame and an ophthalmic optical lens according to any one of claims 1 to 9, the ophthalmic optical lens being secured to the frame.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311375940.4A CN117572662A (en) | 2023-10-20 | 2023-10-20 | Optical lens for eye vision and glasses |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311375940.4A CN117572662A (en) | 2023-10-20 | 2023-10-20 | Optical lens for eye vision and glasses |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN117572662A true CN117572662A (en) | 2024-02-20 |
Family
ID=89887095
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202311375940.4A Pending CN117572662A (en) | 2023-10-20 | 2023-10-20 | Optical lens for eye vision and glasses |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN117572662A (en) |
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2023
- 2023-10-20 CN CN202311375940.4A patent/CN117572662A/en active Pending
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