CN119126408B - A large optical zone intraocular lens based on edge phase technology - Google Patents
A large optical zone intraocular lens based on edge phase technology Download PDFInfo
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- 230000003287 optical effect Effects 0.000 title claims abstract description 59
- 238000002513 implantation Methods 0.000 claims abstract description 10
- 210000001525 retina Anatomy 0.000 claims abstract description 5
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 12
- 230000000694 effects Effects 0.000 abstract description 8
- 230000000007 visual effect Effects 0.000 abstract description 7
- 210000000695 crystalline len Anatomy 0.000 description 87
- 230000000052 comparative effect Effects 0.000 description 8
- 238000003384 imaging method Methods 0.000 description 8
- 238000000034 method Methods 0.000 description 7
- 208000001491 myopia Diseases 0.000 description 6
- 206010052128 Glare Diseases 0.000 description 5
- 210000004087 cornea Anatomy 0.000 description 5
- 238000002474 experimental method Methods 0.000 description 4
- 230000004313 glare Effects 0.000 description 4
- 230000004379 myopia Effects 0.000 description 4
- 238000012360 testing method Methods 0.000 description 4
- 210000001742 aqueous humor Anatomy 0.000 description 3
- 238000012937 correction Methods 0.000 description 3
- 239000013078 crystal Substances 0.000 description 3
- 238000010586 diagram Methods 0.000 description 3
- 230000004402 high myopia Effects 0.000 description 3
- 210000001747 pupil Anatomy 0.000 description 3
- 238000004088 simulation Methods 0.000 description 3
- 238000001356 surgical procedure Methods 0.000 description 3
- 206010047571 Visual impairment Diseases 0.000 description 2
- 230000001886 ciliary effect Effects 0.000 description 2
- 238000013461 design Methods 0.000 description 2
- 238000005457 optimization Methods 0.000 description 2
- 210000001519 tissue Anatomy 0.000 description 2
- 208000029091 Refraction disease Diseases 0.000 description 1
- 230000006978 adaptation Effects 0.000 description 1
- 230000004075 alteration Effects 0.000 description 1
- 230000004430 ametropia Effects 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 230000007423 decrease Effects 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 238000011161 development Methods 0.000 description 1
- 230000004438 eyesight Effects 0.000 description 1
- 239000011521 glass Substances 0.000 description 1
- 230000006872 improvement Effects 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000011056 performance test Methods 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
- 229920000193 polymethacrylate Polymers 0.000 description 1
- 230000008569 process Effects 0.000 description 1
- 230000002035 prolonged effect Effects 0.000 description 1
- 208000014733 refractive error Diseases 0.000 description 1
- 230000002207 retinal effect Effects 0.000 description 1
- 230000004287 retinal location Effects 0.000 description 1
- 230000002441 reversible effect Effects 0.000 description 1
- 230000000630 rising effect Effects 0.000 description 1
- 238000009751 slip forming Methods 0.000 description 1
- 208000005494 xerophthalmia Diseases 0.000 description 1
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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
- G02C7/024—Methods of designing ophthalmic 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
- G02C7/04—Contact lenses for the eyes
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- General Health & Medical Sciences (AREA)
- General Physics & Mathematics (AREA)
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Abstract
本发明公开了一种基于边缘相位技术的大光学区眼内透镜，具体涉及眼内透镜的领域，所述眼内透镜包括眼内透镜主体和板式支撑襻；所述眼内透镜主体包括提供光场调制的镜片光学区，所述板式支撑襻布置在所述镜片光学区的边缘，所述板式支撑襻所在的平面与所述眼内透镜主体所在的平面呈一定夹角；所述镜片光学区包括两个光学面组成的平凹型透镜，所述平凹型透镜植入眼后靠近虹膜的前表面为平面，所述平凹型透镜植入眼后靠近自然晶状体的表面为后表面；所述后表面为具有光场调制能力的相位透镜，光场透过透镜在视网膜位置成像。本发具有提高暗视野视觉质量的效果。
The present invention discloses a large optical zone intraocular lens based on edge phase technology, and specifically relates to the field of intraocular lenses, wherein the intraocular lens comprises an intraocular lens body and a plate-type support haptic; the intraocular lens body comprises a lens optical zone providing light field modulation, the plate-type support haptic is arranged at the edge of the lens optical zone, and the plane where the plate-type support haptic is located forms a certain angle with the plane where the intraocular lens body is located; the lens optical zone comprises a plano-concave lens composed of two optical surfaces, the front surface of the plano-concave lens close to the iris after implantation into the eye is a plane, and the surface of the plano-concave lens close to the natural lens after implantation into the eye is a rear surface; the rear surface is a phase lens with light field modulation capability, and the light field is imaged at the retina through the lens. The invention has the effect of improving the visual quality of dark field.
Description
Technical Field
The invention relates to the technical field of intraocular lenses, in particular to a large optical zone intraocular lens based on an edge phase technology.
Background
At present, the intraocular lens implantation operation of the crystalline eye is an operation mode for correcting myopia, which is compatible with excimer laser operation in the refractive operation market, and is suitable for all myopic operation patients, especially for patients with cornea being too thin, xerophthalmia, high myopia of 600 degrees or more and high requirements on visual quality. The implanted myopic lens is implanted in ciliary sulcus between iris and natural crystalline lens of human eye, can treat ametropia, has very good treatment effect for patients with the need of taking off glasses and high myopia, has good biocompatibility, and has been widely verified in effectiveness and safety.
The operation is characterized in that the cornea is not cut, the shape of the natural cornea is maintained, the operation is safe and reversible, the near vision mirror can be taken out from the human eyes at any time, and the vision quality is high. With the future development trend that intraocular lens implantation surgery is refractive surgery, ICL is accepted by more and more people as a way of myopia correction in recent years along with the standardization of surgery and the further improvement of corresponding safety, more people choose the way to correct myopia in the future, the price of a single product in the future gradually decreases along with the appearance of domestic brands, more myopic patients can choose the product, the proportion of the product in myopia correction gradually increases, and the sales volume can be expected to keep a higher growth situation for a long time in the future.
However, in the dark-field environment, especially when the pupil of the patient is relatively large, the EVO ICL may generate optical interference like halation and glare, which reduces the visual quality and life experience of the patient, and for most patients, the adaptability of the product is further prolonged, and the confidence of the patient for such products is affected.
Disclosure of Invention
In view of the shortcomings of the prior art, the invention aims to provide a large optical zone intraocular lens based on an edge phase technique.
The above object of the present invention is achieved by the following technical solutions:
a large optical zone intraocular lens based on edge phase technology, comprising an intraocular lens body and plate type supporting loop;
the intraocular lens main body comprises a lens optical area for providing light field modulation, the plate type supporting loop is arranged at the edge of the lens optical area, and a certain included angle is formed between the plane of the plate type supporting loop and the plane of the intraocular lens main body;
The lens optical zone comprises a plano-concave lens formed by two optical surfaces, the front surface of the plano-concave lens, which is close to the iris after being implanted into the eye, is a plane, and the surface of the plano-concave lens, which is close to the natural crystalline lens after being implanted into the eye, is a rear surface;
The back surface is a phase lens with light field modulation capability, and the light field is imaged at the retinal position through the lens.
Further, the phase lens is formed by combining (i, j) phase structures in a certain period, and the phase function of the phase lens in a single period is determined according to the following formula (1):
Hi(r)＝Ai-Bi×tan-1[-1/2+1/2cos[π(r2-ri1 2)/(rj 2-ri1 2)]],i＝1…N,N Is an integer, j=1..M, M is an integer, (1)
Wherein, the above formula (1) uses the vertex of the optical surface as the origin O, uses the optical axis as the coordinate Z axis, establishes an arbitrary spatial polar coordinate system, r is a radial coordinate, r i1 is a phase initial coordinate, r j is an end phase coordinate, N is the maximum number of edge phase structures, a i is a reference phase coefficient of the ith phase structure, and B i is a phase modulation amplitude of the ith phase structure;
The range of the reference phase coefficient A of the phase lens of the lens optical area is 0-100;
the range of the phase modulation amplitude B of the phase lens of the lens optical area is 0-1;
the maximum edge phase structure number N of the phase lens of the lens optical area is in the range of 0-10;
H i (r) ranges from 0 to 22.7.
Further, at least a portion of the micro-phase structure has a size in the range of 0.5 to 5 times the incident wavelength.
Further, the lens optical area is a combined phase lens, and the radial width of the lens optical area ranges from 1mm to 8mm.
Further, A ranges from 0 to 24.
Further, B is in the range of 0.3 to 0.6.
Further, the range of N is 2-6.
Further, the size of the microphase structure is in the range of 0.5 to 2 times the incident wavelength.
Further, the refractive index of the lens optical area and the plate-type supporting loop is 1.4-1.6, and the water content is 8% -60%.
Further, at least one circular water guide hole is distributed on the periphery of the optical area of the lens, and the diameter range of the circular water guide hole is 0.2-0.4 mm.
Compared with the prior art, the invention has the beneficial effects that:
According to the invention, an edge phase technology is adopted for the first time, so that the imaging quality of a patient in a dark environment and under the condition of large pupils is greatly improved.
Drawings
FIG. 1 is a schematic diagram of an intraocular lens based on the edge phase technique and implanted into a LeGrand simplified eye model according to embodiment 1 of the present invention;
FIG. 2 is a schematic top view of an intraocular lens according to embodiment 1 of the present invention;
FIG. 3 is a schematic side view of an intraocular lens according to embodiment 1 of the present invention;
FIG. 4 is a graph showing the initial phase distribution of microstructures in a single period for an intraocular lens according to example 1 of the present invention based on the fringe phase technique;
FIG. 5 is a graph showing the distribution of the addition of the edge phase during a single period for an intraocular lens according to embodiment 2 of the present invention;
Fig. 6 is a graph of MTF imaging quality and effect after implantation of a-16D lens of comparative example 1 in an LB model eye with a 5mm aperture.
Fig. 7 is a graph showing MTF imaging quality and effect after implantation of a-16D lens, 5mm aperture, in an LB model eye, of an implantable posterior chamber type myopic intraocular lens in accordance with example 1 of the present invention.
Fig. 8 is a graph of glare contrast experiments for the intraocular lenses of comparative example 1 and example 1 at 5mm aperture in an ISO model eye.
Fig. 9 is a graph comparing MTF curves of the intraocular lenses of comparative example 1 and example 1 at 5mm aperture in an ISO model eye.
Reference numerals 1, cornea, 2, intraocular lens, 3, natural lens, 4, optic zone of lens, 5, plate type supporting loop and 6, water guide hole.
Detailed Description
The present invention will be described in detail with reference to examples.
Example 1
The embodiment 1 of the invention discloses a large optical zone intraocular lens based on edge phase technology, which comprises an intraocular lens main body and plate type supporting loop;
The intraocular lens body comprises a lens optical area for providing light field modulation, plate-type supporting loop is arranged at the edge of the lens optical area, and a certain included angle is formed between the plane of the plate-type supporting loop and the plane of the intraocular lens body;
the lens optical zone comprises a plano-concave lens formed by two optical surfaces, the front surface of the plano-concave lens, which is close to the iris after being implanted into the eye, is a plane, and the surface of the plano-concave lens, which is close to the natural lens after being implanted into the eye, is a rear surface;
the back surface is a phase lens with light field modulation capability, through which the light field is imaged at the retinal location.
Fig. 1 shows a light field distribution state of a large optical zone intraocular lens based on the edge phase technique disclosed in embodiment 1 of the present invention in a Le Grand simplified eye model, the optical characteristics of cornea 1 are described by using the simplified eye model, the parameters of the whole eye model are shown in table 1, an implantable near-sighted intraocular lens 2 is inserted in front of a natural lens 3, the front surface is set to be a plane, the rear surface is a phase lens surface, and the parameters of the whole combined system are shown in table 2. The intraocular lens 2 of example 1 was made of hydrophilic polymethacrylate, and had a refractive index of 1.442, an Abbe number of 50, a design optical power of-16D, a design wavelength λ of 0.546um, an optical zone diameter of 6.0mm, and a center thickness of 0.13mm.
In some optional implementations of some embodiments, at least one circular water guide hole is distributed around the optical area of the lens, and the diameter of the circular water guide hole ranges from 0.2mm to 0.4mm. The diameter of the circular water guiding hole in example 1 was 0.2mm.
Figures 2 and 3 are top and side views, respectively, of an intraocular lens of example 1, from which it can be seen that the aperture in the center of the optic zone is primarily responsible for circulation and circulation of aqueous humor, with the two apertures in the haptic corners serving to distinguish the anterior and posterior sides of the lens. In order to ensure better aqueous humor circulation at the edge of the iris, 4 water guide holes 6 are added, so that the aqueous humor circulation is smoother after the pupil is enlarged. From a side view, the slope of the plate haptics is substantially at an angle to the angle of the chamber to ensure that the haptics of the lens do not contact the iris tissue of the human eye and that the haptic angles are inserted into tissue adjacent the ciliary sulcus to act as an intraocular lens fixation.
Table 1Le Grand simplified eye model parameter table
Table 2 model parameters table after intraocular lens implantation
In some alternative implementations of some embodiments, the lens optic zone phase structure is formed by a combination of (i, j) phase structures for a certain period, wherein the phase function of the phase lens in a single period is determined according to the following equation (1):
Hi(r)＝Ai-Bi×tan-1[-1/2+1/2cos[π(r2-ri1 2)/(rj 2-ri1 2)]],i＝1…N,N Is an integer, j=1..M, M is an integer, (1)
Wherein, the formula (1) uses the vertex of the optical surface as the origin O, uses the optical axis as the coordinate Z axis, establishes an arbitrary space polar coordinate system, r is a radial coordinate, r i1 is a phase initial coordinate, r j is an end phase coordinate, N is the maximum edge phase structure number, A i is the reference phase coefficient of the ith phase structure, B i is the phase modulation amplitude of the ith phase structure, i is the number of phase structures, j is the end point of the phase structure, H i (r) is the phase function about the radial coordinate r;
The maximum phase difference for the ith phase structure is determined by the following formula, where RI icl is the refractive index of the phase altering lens and RI aqueous is the refractive index of the surrounding medium, i.e. aqueous:
Phase_wavei＝Hi(r)×(RIicl-RIaqueous)/0.546
In order to enable the phase lens to provide a certain refractive power, the reference phase coefficient and the modulation amplitude of the ith microstructure need to be calculated through an optimization algorithm in a single period so as to meet the high refractive efficiency and diopter and other aberration correction capabilities, and meanwhile, new micro-phase structures need to be added to the edge of the original micro-phase structure continuously in the optimization process, namely the number of i is increased continuously, iteration is performed continuously, and finally the expected purpose is achieved. In some optional implementations of some embodiments, the reference phase coefficient a of the lens optical zone phase lens ranges from 0 to 100, preferably, a ranges from 0 to 24. The phase modulation amplitude B of the phase lens ranges from 0 to 1, preferably B ranges from 0.3 to 0.6. H i (r) ranges from 0 to 22.7, preferably from 0 to 5. Some micro-phase structures have a size in the range of 0.5 to 5 times the incident wavelength, preferably 0.5 to 2 times the incident wavelength, and exhibit significant vector light field characteristics, and in some alternative implementations of some embodiments, the maximum edge phase structure number N of the phase lens of the lens optic zone ranges from 0 to 10, preferably N ranges from 2 to 6. In some alternative implementations of some embodiments, the optic zone of the optic and the plate haptics have refractive indices of 1.4-1.6 and a water content of 8% -60%. In some alternative implementations of some embodiments, the optic zone is a combination phase lens, and the optic zone has a radial width in the range of 1mm to 8mm.
The phase function (type I phase) of the phase lens of example 1 in a single period is shown in fig. 4, and the maximum edge phase structure number N of the phase lens is 1.
Example 2 differs from example 1 in that the maximum edge phase structure number N of the phase lens is 1, the phase function (type II phase) of the phase lens of example 2 in a single period is as shown in figure 5,
The I-phase of fig. 4 is a continuous phase distribution, and the smoothly rising phase distribution and the gradually decreasing phase distribution are asymmetric, so that the light incident on the edge is convenient, and the light has higher energy at a designated position, so that the degree of freedom is increased, and the effect of pertinently adjusting the energy is achieved.
Fig. 5 is a schematic diagram of a phase distribution structure, in which a spatially discrete phase distribution structure is continuously formed at the edge of a single period by continuously and iteratively adding an I-type phase to the edge of the I-type phase on the basis of the I-type phase distribution, i.e., a II-type phase distribution structure is constructed, the phase height and symmetry of the superimposed phase structure can be freely adjusted and set, the phase adjustment capability of a single I-type phase on the phase is limited, the degree of freedom is only reflected in the depth direction, and the distribution state of the incident light energy intensity incident into the region can be more flexibly controlled after the II-type phase distribution is constructed in the single period.
Comparative example
Comparative example 1 an EVO ICL type intraocular lens currently commercially available was used.
Detection method
Curing Performance test
1. MTF imaging quality and effect map testing
FIG. 6 is a graph of MTF imaging quality and effect after implantation of an EVO ICL-16D crystal (comparative example 1) in a Le Grand model eye, 5mm aperture. As can be seen from fig. 6, when the Le Grand model eye is used for simulation, the aperture is increased to 5mm, the condition of dark environment is simulated, the MTF is at low frequency, about 10lp/mm, there is obvious recess, this position corresponds to the area where the human eye is most sensitive to contrast, the patient can feel obvious visual disturbance, as can be seen from the dot diagram on the right side, a circle of obvious halation appears around the central strong light spot, which explains why the patient, especially the patient with high myopia, has obvious halation disturbance after the EVO ICL is implanted, because the light of the central point can be well focused on the retina to form clear imaging, but the peripheral light can not provide diopter due to the limitation of the effective optical area, thereby forming focusing in front of the retina to cause visual disturbance.
Fig. 7 is a graph showing the imaging quality and effect of MTF after the eye with a Le Grand model is implanted with a 5mm aperture, sea ICL-16D crystal (example 1), and it can be seen from fig. 7 that the aperture is also increased to 5mm by simulating the eye with a Le Grand model, and the MTF is in a dark environment, so that after the eye is implanted with such an intraocular lens, it is conceivable that no visual interference such as halation occurs, and no visible halation occurs around the strong center, and the light rays at the center and periphery are very well focused on the retina, as demonstrated by the actual imaging optical path graph, and therefore, due to the introduction of the edge phase technique, the visual interference is greatly reduced, and the visual quality is improved.
2. Glare contrast experiment
Fig. 8 is a graph of an EVO ICL (comparative example 1) and a SEAT ICL (example 1) glare contrast experiment at 5mm aperture in an ISO model eye, the experiment test uses a standard ISO eye model, the test aperture is 5mm for testing dark environment, the diopter of the crystal is-16D, the graph is very close to theoretical simulation, for EVO ICL, a few circles of very obvious halation appears around a central bright spot, and for SEAT ICL, no aperture is around, and focusing is very clear. This also demonstrates from one aspect that implantable intraocular lenses based on fringe phase techniques greatly improve night glare.
3. Comparison of MTF Curve
Fig. 9 is a graph comparing MTF curves of EVO ICL (comparative example 1) and SEAT ICL (example 1) at 5mm aperture in an ISO model eye, which is a result of actual measurement using a standard ISO model eye, and 5mm aperture size, as well as a very effective tool for evaluating visual quality, unlike a theoretical simulation, in which it can be seen that a significant depression is seen for EVO ICL at its low frequency position, which is also one of the causes of halation generation, but for SEAT ICL, the curve is very smooth and has no abrupt change.
The above description is only a preferred embodiment of the present invention, and the protection scope of the present invention is not limited to the above examples, and all technical solutions belonging to the concept of the present invention belong to the protection scope of the present invention. It should be noted that modifications and adaptations to the present invention may occur to one skilled in the art without departing from the principles of the present invention and are intended to be within the scope of the present invention.
Claims (7)
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| CN113040976A (en) * | 2021-03-04 | 2021-06-29 | 天津世纪康泰生物医学工程有限公司 | Ultrathin zero-spherical-aberration implantable myopia lens |
| CN113693779A (en) * | 2021-06-01 | 2021-11-26 | 天津世纪康泰生物医学工程有限公司 | Diffraction type multifocal intraocular lens with targeted light field distribution |
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| US20070282438A1 (en) * | 2006-05-31 | 2007-12-06 | Xin Hong | Intraocular lenses with enhanced off-axis visual performance |
| ES2667277T3 (en) * | 2010-02-17 | 2018-05-10 | Akkolens International B.V. | Adjustable chiral ophthalmic lenses |
| JP5993950B2 (en) * | 2012-12-14 | 2016-09-21 | 株式会社メニコン | Diffractive multifocal ophthalmic lens and manufacturing method thereof |
| CN116507966A (en) * | 2020-08-21 | 2023-07-28 | 华柏恩视觉研究中心有限公司 | Ophthalmic devices, systems and/or methods for managing ocular conditions and/or reducing night vision impairment |
| US20250085569A1 (en) * | 2022-01-14 | 2025-03-13 | Ast Products, Inc. | Aspheric phase-ring structured lens designs, manufacture, and uses thereof |
| CN114779497B (en) * | 2022-05-09 | 2024-05-10 | 天津世纪康泰生物医学工程有限公司 | A scleral contact lens based on phase modulation technology |
| CN115721448B (en) * | 2022-11-22 | 2023-10-31 | 无锡蕾明视康科技有限公司 | Full vision range type artificial lens |
| CN116035762A (en) * | 2023-02-22 | 2023-05-02 | 南开大学 | Intraocular lens for correcting peripheral visual field aberration |
| CN117503426A (en) * | 2023-08-28 | 2024-02-06 | 上海晶伟尔医疗科技有限公司 | A posterior chamber intraocular lens based on a tapered lens |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN113040976A (en) * | 2021-03-04 | 2021-06-29 | 天津世纪康泰生物医学工程有限公司 | Ultrathin zero-spherical-aberration implantable myopia lens |
| CN113693779A (en) * | 2021-06-01 | 2021-11-26 | 天津世纪康泰生物医学工程有限公司 | Diffraction type multifocal intraocular lens with targeted light field distribution |
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