Large-optical-zone intraocular lens based on edge phase technology
By introducing edge phase technology into the intraocular lens and optimizing the light field modulation, the problems of halo and glare interference in dark vision environments are solved, thus improving the visual quality of patients.
Patent Information
- Authority / Receiving Office
- WO · WO
- Patent Type
- Applications
- Current Assignee / Owner
- SHANGHAI JINGWEIER MEDICAL TECHNOLOGY CO
- Filing Date
- 2025-08-21
- Publication Date
- 2026-05-21
AI Technical Summary
Traditional intraocular lenses are prone to optical interference such as halos and glare in dark environments, especially with large pupils, which can affect patients' visual quality and daily life experience.
An intraocular lens employing edge-phase technology optimizes light field modulation capabilities by introducing multiple phase structures into the lens's optical zone, thereby increasing the detail of microstructures and phase modulation capabilities, and improving imaging quality in low-light environments.
It significantly reduces halos and glare interference in dark environments, improving patients' visual quality.
Smart Images
Figure CN2025116232_21052026_PF_FP_ABST
Abstract
Description
A large optical zone intraocular lens based on edge phase technology Technical Field
[0001] This invention relates to the technical field of intraocular lenses, and in particular to a large optical zone intraocular lens based on edge phase technology. Background Technology
[0002] According to a 2018 research report released by the World Health Organization, China currently has as many as 600 million people with myopia, almost half of the country's total population, making it the country with the highest proportion of myopic individuals in the world. Currently, the incidence of myopia is increasing year by year with age, both in urban and rural areas. The average incidence of myopia among primary school students has reached as high as 31.67%, and by high school, almost 80% of students suffer from varying degrees of vision problems. More seriously, pathological myopia can lead to blindness and low vision, posing a huge threat to future career choices and even daily life. According to calculations in the 2012 "National Visual Health Report," the socioeconomic cost caused by various visual impairments was over 680 billion yuan, accounting for as much as 1.3% of that year's GDP. Including the loss of quality of life due to visual health issues, the proportion reaches 1.83% of GDP.
[0003] Phacobonic intraocular lens (IOL) implantation surgery is a refractive surgery method for correcting myopia, on par with excimer laser surgery. It is suitable for all myopia patients, especially those with thin corneas, dry eye syndrome, high myopia (over 600 degrees), and those with high visual quality requirements. The implantable IOL is placed in the ciliary sulcus between the iris and the natural lens of the eye. It can treat refractive errors and has excellent therapeutic effects for patients who want to be free of glasses and for those with high myopia. The lenses have good biocompatibility, and their effectiveness and safety have been widely verified.
[0004] The characteristics of this surgery are: it does not cut the cornea, maintains the natural shape of the cornea, is safe and reversible, allows for the removal of glasses at any time, and provides high visual quality. Phacokinetic intraocular lens (ICL) implantation is the future trend of refractive surgery. With the standardization of the procedure and further improvements in safety, especially in recent years, ICL has become increasingly accepted as a method of myopia correction. More people will choose this method to correct myopia in the future. With the emergence of domestic brands, the price of individual products will gradually decrease, allowing more myopia patients to choose these products. The proportion of these products in myopia correction will gradually increase, and it is foreseeable that sales will maintain a high growth trend for a long time to come.
[0005] However, in dark environments, especially when the patient's pupils are large, traditional technical solutions can cause optical interference such as halos and glare with the EVO ICL, which reduces the patient's visual quality and life experience. For most patients, the adaptation period for this product is further prolonged, affecting their confidence in this type of product. Summary of the Invention
[0006] To address the shortcomings of existing technologies, the present invention aims to provide a large optical zone intraocular lens based on edge phase technology.
[0007] The above-mentioned objective of the present invention is achieved through the following technical solution:
[0008] An intraocular lens with a large optical zone based on edge phase technology includes an intraocular lens body and a plate-type support haptic.
[0009] The intraocular lens body includes a lens optical area that provides light field modulation, and the plate-type support haptic is arranged at the edge of the lens optical area. The plane where the plate-type support haptic is located forms a certain angle with the plane where the intraocular lens body is located.
[0010] The optical area of the lens includes a plano-concave lens composed of two optical surfaces. After the plano-concave lens is implanted into the eye, the anterior surface near the iris is a plane, and the posterior surface near the natural lens is the posterior surface.
[0011] The rear surface is a phase lens with light field modulation capability, and the light field is imaged at the retina position through the lens.
[0012] Furthermore, the phase lens is formed by combining (i,j) phase structures within a certain period, and the phase function of the phase lens within a single period is determined according to the following formula (1):
[0013] H i (r)=A i -B i *tan -1 [-1 / 2+1 / 2cos[π(r 2 -r i1 2 ) / (r j 2 -r i1 2 )]],i=1…N,N is an integer,j=1…M,M is an integer;(1)
[0014] In formula (1), an arbitrary spatial polar coordinate system is established with the vertex of the optical surface as the origin O and the optical axis as the Z-axis. r is the radial coordinate. i1 It is the initial phase coordinate, r jIt is the endpoint phase coordinate, N is the number of maximum edge phase structures, A i B is the reference phase coefficient of the i-th phase structure. i It is the phase modulation amplitude of the i-th phase structure; i refers to the nth phase structure, j refers to the end point of the phase structure; Hi(r) refers to the phase function with respect to the radial coordinate r;
[0015] The reference phase coefficient A of the phase lens in the optical region of the lens is in the range of 0 to 100;
[0016] The phase modulation amplitude B of the phase lens in the optical region of the lens is between 0 and 1.
[0017] The maximum number N of edge phase structures of the phase lens in the optical region of the lens ranges from 0 to 10.
[0018] H i (r) ranges from 0 to 22.7.
[0019] Furthermore, at least some of the microphase structure dimensions are in the range of 0.5 to 5 times the incident wavelength.
[0020] Furthermore, the optical region of the lens is a combined phase lens, and the radial width of the optical region of the lens ranges from 1mm to 8mm.
[0021] Furthermore, the range of A is between 0 and 24.
[0022] Furthermore, B ranges from 0.3 to 0.6.
[0023] Furthermore, N ranges from 2 to 6.
[0024] Furthermore, the micro-phase structure size is in the range of 0.5 to 2 times the incident wavelength.
[0025] Furthermore, the refractive index of the lens optical region and the plate support haptic is 1.4 to 1.6, and the water content is 8% to 60%.
[0026] Furthermore, 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 0.2 to 0.4 mm.
[0027] Compared with the prior art, the beneficial effects of the present invention are:
[0028] This invention patent is the first to use edge phase technology, which significantly improves the imaging quality of patients in dark environments and with large pupils. In the process of optimizing the single-cycle phase structure, this technology continuously adds new micro-phase structures at the edge of the initial micro-phase structure, thereby increasing the detail of the microstructure and the phase modulation capability, and ultimately improving the visual quality of dark vision. Attached Figure Description
[0029] Figure 1 is a schematic diagram of an intraocular lens based on edge phase technology and implanted in a simplified Le Grand eye model disclosed in Embodiment 1 of the present invention;
[0030] Figure 2 is a top view of an intraocular lens based on edge phase technology disclosed in Embodiment 1 of the present invention;
[0031] Figure 3 is a side view schematic diagram of an intraocular lens based on edge phase technology disclosed in Embodiment 1 of the present invention;
[0032] Figure 4 shows the initial phase distribution of the microstructure within a single cycle of an intraocular lens based on edge phase technology disclosed in Embodiment 1 of the present invention.
[0033] Figure 5 is a distribution diagram of an intraocular lens based on edge phase technology disclosed in Embodiment 2 of the present invention after adding edge phase within a single cycle;
[0034] Figure 6 shows the MTF imaging quality and effect of the intraocular lens of Comparative Example 1 after implantation of a 5mm aperture, -16D lens in the eye of the LB model.
[0035] Figure 7 shows the MTF imaging quality and effect of an implantable posterior chamber myopic intraocular lens based on edge phase technology disclosed in Embodiment 1 of the present invention after implantation of a 5mm aperture, -16D lens in an LB model eye.
[0036] Figure 8 shows a comparison experiment of glare from the intraocular lenses of Comparative Example 1 and Example 1 in the ISO model eye at a 5mm aperture.
[0037] Figure 9 is a comparison of the MTF curves of the intraocular lenses of Comparative Example 1 and Example 1 at a 5mm aperture in the ISO model eye.
[0038] Reference numerals: 1. Cornea; 2. Intraocular lens; 3. Natural lens; 4. Lens optical zone; 5. Plate support haptic; 6. Aqueduct. Detailed Implementation
[0039] The present invention will now be described in detail with reference to the embodiments.
[0040] Example 1
[0041] Embodiment 1 of the present invention discloses a large optical zone intraocular lens based on edge phase technology, comprising an intraocular lens body and a plate-type support haptic;
[0042] The intraocular lens body includes a lens optical area that provides light field modulation, and a plate-type support haptic is arranged at the edge of the lens optical area. The plane where the plate-type support haptic is located forms a certain angle with the plane where the intraocular lens body is located.
[0043] The optical zone of the lens includes a plano-concave lens composed of two optical surfaces. After the plano-concave lens is implanted in the eye, the anterior surface near the iris is the planar surface, and the surface near the natural lens is the posterior surface.
[0044] The rear surface is a phase lens with light field modulation capability, and the light field is imaged at the retina position through the lens.
[0045] Figure 1 shows the light field distribution of a large optical zone intraocular lens based on edge phase technology disclosed in Embodiment 1 of the present invention in a simplified Le Grand eye model. A simplified eye model is used to describe the optical characteristics of the cornea 1. The parameters of the entire eye model are shown in Table 1. An implantable myopic intraocular lens 2 is inserted in front of the natural lens 3, with the anterior surface set as a plane and the posterior surface as a phase lens surface. The parameters of the entire combined system are shown in Table 2. The intraocular lens 2 of Embodiment 1 is made of hydrophilic polymethyl methacrylate with a refractive index of 1.442 and an Abbe number of 50; the designed optical power is -16D; the designed wavelength λ is 0.546 μm; the optical zone diameter is 6.0 mm; and the center thickness is 0.13 mm.
[0046] In some optional implementations of certain embodiments, at least one circular water guide hole is distributed around the periphery of the lens optical region, and the diameter of the circular water guide hole ranges from 0.2 to 0.4 mm. In Embodiment 1, the diameter of the circular water guide hole is 0.2 mm.
[0047] Figures 2 and 3 are the top and side views of the intraocular lens of Example 1, respectively. As can be seen from the figures, the central aperture in the optical zone is primarily responsible for the circulation and flow of aqueous humor, while the two apertures at the haptic angles distinguish the front and back of the lens. To ensure better aqueous humor flow at the iris edge, four additional drainage holes (6) are added to further ensure smoother aqueous humor flow after pupil enlargement. The side view shows that the slope of the plate haptic essentially forms a certain angle with the iris angle, ensuring that the lens haptic does not contact the iris tissue of the human eye. The haptic angles insert into the tissue near the ciliary sulcus, serving to fix the artificial lens.
[0048] Table 1. Parameters of Le Grand's Simplified Eye Model
[0049] Table 2. Model parameters after implantation of intraocular lens
[0050] In some alternative implementations of some embodiments, the phase structure of the lens optical region is formed by a combination of (i,j) phase structures within a certain period, wherein the phase function of the phase lens within a single period is determined according to the following formula (1):
[0051] H i (r)=A i -B i *tan -1 [-1 / 2+1 / 2cos[π(r 2 -r i1 2 ) / (r j 2 -r i1 2 )]],i=1…N,N is an integer,j=1…M,M is an integer;(1)
[0052] In formula (1), an arbitrary spatial polar coordinate system is established with the vertex of the optical surface as the origin O and the optical axis as the Z-axis. r is the radial coordinate. i1 It is the initial phase coordinate, r j It is the endpoint phase coordinate, N is the number of maximum edge phase structures, A i B is the reference phase coefficient of the i-th phase structure. i It is the phase modulation amplitude of the i-th phase structure; i refers to the nth phase structure, j refers to the end point of the phase structure; Hi(r) refers to the phase function with respect to the radial coordinate r;
[0053] The maximum phase difference of the i-th phase structure is determined by the following formula, where RI icl It refers to the refractive index, RI, of the phase-changing lens. aqueous The refractive index of the surrounding medium, i.e., the aqueous humor:
[0054] Phase_wave i =H i (r)*(RI icl -RI aqueous ) / 0.546
[0055] To enable the phase lens to provide a certain refractive power, within a single cycle, an optimization algorithm is needed to calculate the reference phase coefficient and modulation amplitude of the i-th microstructure. This ensures that it simultaneously satisfies high refractive efficiency, refractive power, and other aberration correction capabilities. Furthermore, the optimization process involves continuously adding new micro-phase structures to the edges of the original micro-phase structure, i.e., continuously increasing the number of microstructures (i), iterating repeatedly until the desired result is achieved. In some optional implementations of certain embodiments, the reference phase coefficient A of the phase lens in the optical region of the lens ranges from 0 to 100, preferably from 0 to 24. The phase modulation amplitude B of the phase lens ranges from 0 to 1, preferably from 0.3 to 0.6. i The range of (r) is between 0 and 22.7, preferably between 0 and 5. Some micro-phase structure sizes are in the range of 0.5 to 5 times the incident wavelength, preferably between 0.5 and 2 times the incident wavelength, exhibiting significant vector light field characteristics. In some optional implementations of some embodiments, the maximum number N of edge phase structures in the phase lens of the lens optical region ranges from 0 to 10, preferably between 2 and 6. In some optional implementations of some embodiments, the refractive index of the lens optical region and the plate support loop is 1.4 to 1.6, and the water content is 8% to 60%. In some optional implementations of some embodiments, the lens optical region is a combined phase lens, and the radial width of the lens optical region ranges from 1 mm to 8 mm.
[0056] The phase function (Type I phase) of the phase lens in Example 1 within a single period is shown in Figure 4. The maximum number of edge phase structures N of the phase lens is 1.
[0057] The difference between Example 2 and Example 1 is that the number N of the maximum edge phase structure of the phase lens in Example 2 is 1. The phase function (Type II phase) of the phase lens in a single period of Example 2 is shown in Figure 5.
[0058] The Type I phase in Figure 4 is a continuous phase distribution. The smoothly rising phase distribution and the gradually decreasing phase distribution are not symmetrical, which makes it convenient for light rays incident on the edge to have relatively high energy at a specified position, increasing the degree of freedom and allowing for targeted energy adjustment.
[0059] Figure 5 shows that, based on the type I phase distribution, by iteratively adding type I phases to the edges of the type I phase, a spatially discrete phase distribution structure is continuously formed at the edges of a single cycle, thus constructing a type II phase distribution structure. The phase height and symmetry of the superimposed phase structure can be freely adjusted and set. The ability of a single type I phase to adjust the phase is limited, and the degree of freedom is only reflected in the depth direction. After constructing the type II phase distribution within a single cycle, the energy intensity and distribution state of the incident light incident on this region can be controlled more flexibly.
[0060] Comparative Example
[0061] Comparative Example 1 uses the currently commercially available EVO ICL type intraocular lens.
[0062] Detection methods
[0063] Curing performance test
[0064] 1. MTF imaging quality and effect diagram test
[0065] Figure 6 shows the MTF imaging quality and effect after implantation of the EVO ICL-16D lens (Comparative Example 1) with a 5mm aperture in the Le Grand model eye. As can be seen from Figure 6, using the Le Grand model eye for simulation, with the aperture increased to 5mm to simulate a dark environment, the MTF at low frequencies, approximately 10 lp / mm, exhibits a noticeable concavity. This location corresponds precisely to the area of highest contrast sensitivity in the human eye, causing significant visual interference for patients. The dot plot on the right shows a distinct halo around the central bright spot. This explains why patients, especially those with high myopia, experience significant halo interference after EVO ICL implantation. While the light from the central point can focus well on the retina to form a relatively clear image, the surrounding light, limited by the effective optical zone, cannot provide refractive power, thus focusing in front of the retina and causing visual interference.
[0066] Figure 7 shows the MTF imaging quality and effect after implantation of a 5mm aperture SEAT ICL-16D lens (Example 1) in the Le Grand model eye. As can be seen from Figure 7, using the Le Grand model eye for simulation, the aperture was also increased to 5mm to simulate a dark environment. The MTF did not show any indentation at low frequencies. Therefore, it is conceivable that there will be no visual interference such as halos after implantation of this type of intraocular lens. As can be seen from the dot plot, there is no obvious halo around the center. The light from the center and the periphery is very well focused on the retina. The actual imaging optical path diagram also proves this point. Therefore, due to the introduction of edge phase technology, not only is visual interference greatly reduced, but visual quality is also improved.
[0067] 2. Glare Contrast Experiment
[0068] Figure 8 shows a comparison of glare between the EVO ICL (Comparative Example 1) and SEAT ICL (Example 1) in an ISO model eye with a 5mm aperture. The experiment used a standard ISO eye model, with a 5mm aperture chosen for testing in dark environments. The refractive power of both lenses was -16D. As can be seen from the figure, the results are very close to the theoretical simulation. The EVO ICL exhibits several very obvious halos around the central bright spot, while the SEAT ICL shows no halos and excellent focus. This also demonstrates that implantable intraocular lenses based on edge-phase technology significantly improve glare interference at night.
[0069] 3. MTF curve comparison
[0070] Figure 9 shows a comparison of the MTF curves of EVO ICL (Comparative Example 1) and SEAT ICL (Example 1) under a 5mm aperture in the ISO eye model. Unlike the theoretical simulation, this is the result of actual measurement using a standard ISO eye model with a 5mm aperture, also used to simulate a dark environment. The MTF curve is a very effective tool for evaluating visual quality. As can be seen from the figure, for EVO ICL, there is a noticeable dip in its low-frequency position, which is completely consistent with the theoretical simulation. This is also one of the reasons for the halo effect. However, for SEAT ICL, the curve is very smooth and there are no abrupt changes.
[0071] The above description is merely a preferred embodiment of the present invention. The scope of protection of the present invention is not limited to the above embodiments. All technical solutions falling within the scope of the present invention's concept are within the scope of protection of the present invention. It should be noted that for those skilled in the art, any improvements and modifications made without departing from the principles of the present invention should also be considered within the scope of protection of the present invention.
Claims
1. A large optical zone intraocular lens based on edge phase technology, characterized in that, The intraocular lens includes an intraocular lens body and a plate-type support haptic; The intraocular lens body includes a lens optical area that provides light field modulation, and the plate-type support haptic is arranged at the edge of the lens optical area. 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 optical area of the lens includes a plano-concave lens composed of two optical surfaces. After the plano-concave lens is implanted into the eye, the anterior surface near the iris is a plane, and the posterior surface near the natural lens is the posterior surface. The rear surface is a phase lens with light field modulation capability, and the light field is imaged at the retina position through the lens.
2. An intraocular lens based on the edge phase technique with a large optical zone according to claim 1, characterized in that The phase lens is formed by combining (i,j) phase structures within a certain period, and the phase function of the phase lens within a single period is determined according to the following formula (1): H i (r) = A i -B i *tan -1 [-1 / 2 + 1 / 2 cos [π(r 2 -r i1 2 ) / (r j 2 -r i1 2 )]], i = 1...N, N is an integer, j = 1...M, M is an integer; (1) wherein the above formula (1) establishes an arbitrary space polar coordinate system with the vertex of the optical surface as the origin O and the optical axis as the coordinate Z axis, r is the radial coordinate, r i1 is the initial phase coordinate, r j is the terminal phase coordinate, N is the maximum number of edge phase structures, A i is the reference phase coefficient of the i-th phase structure, B i is the phase modulation amplitude of the i-th phase structure; i refers to the phase structure number, j refers to the terminal point of the phase structure; Hi(r) refers to the phase function with respect to the radial coordinate r; The reference phase coefficient A of the phase lens in the optical region of the lens is in the range of 0 to 100; The phase modulation amplitude B of the phase lens in the optical region of the lens is between 0 and 1. The maximum number N of edge phase structures of the phase lens in the optical region of the lens ranges from 0 to 10. H i (r) ranges between 0 and 22.
7.
3. An intraocular lens based on the edge phase technique with a large optical zone according to claim 2, characterized in that At least some of the microphase structure dimensions are in the range of 0.5 to 5 times the incident wavelength.
4. An intraocular lens based on the edge phase technique with a large optical zone according to claim 1, characterized in that, The optical region of the lens is a combined phase lens, and the radial width of the optical region of the lens ranges from 1 mm to 8 mm.
5. An intraocular lens based on the edge phase technique with a large optical zone according to claim 2, characterized in that, The range of A is between 0 and 24.
6. An intraocular lens based on the edge phase technique with a large optical zone according to claim 2, characterized in that, B ranges from 0.3 to 0.
6.
7. An intraocular lens based on the edge phase technique with a large optical zone according to claim 2, characterized in that, N ranges from 2 to 6.
8. An intraocular lens based on the edge phase technique with a large optical zone according to claim 1, characterized in that, The microphase structure size is in the range of 0.5 to 2 times the incident wavelength.
9. An intraocular lens based on the edge phase technique with a large optical zone according to claim 1, characterized in that, The refractive index of the optical region of the lens and the plate-type support haptic is 1.4 to 1.6, and the water content is 8% to 60%.
10. An intraocular lens based on the edge phase technique according to claim 1, characterized in that 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 0.2 to 0.4 mm.