Full-range intraocular lens

Abstract

The present invention discloses a full-visibility intraocular lens, including an optical part, a first support part and a second support part, the optical part, the first support part and the second support part are integrally molded with the same material, the optical part is located between the first support part and the second support part, the optical part is composed of two optical surfaces, the optical surfaces are spherical or aspheric, one of the optical surfaces has a diffractive structure for modulating the optical field distribution of the incident light. The present invention adjusts the optical field distribution of the incident light of the optical part through the diffractive structure, reduces the sharp points on the entire optical surface, effectively reduces glare and reduces chromatic aberration, allows the patient to see more clearly in the full visibility between the foci, and brings the patient a better visual experience.

Description

[Technical field]

[0001] The present invention relates to the technical field of optical devices, and in particular to full-range intraocular lenses. [Background technology]

[0002] An intraocular lens (IOL) is an optical device made of synthetic materials that has been established as a common medical device for replacing the pathologically clouded crystalline lens and restoring vision to cataract patients after surgery. A multifocal intraocular lens is a type of intraocular lens. Multifocal intraocular lenses (IOLs) can provide two or more focal points (e.g., trifocal IOLs provide distance vision, intermediate vision, and near vision), and are commonly implanted in patients' eyes during cataract surgery to replace the pathologically altered crystalline lens. Multifocal IOLs are broadly divided into two types: diffractive and refractive, among which the surface of diffractive multifocal IOLs includes multiple concentric ring-shaped small step gratings that diffract light in multiple directions to form multiple focal points, and the surface of refractive multifocal IOLs may include multiple concentric ring-shaped spherical or aspherical surfaces with different curvatures, or multiple sector-shaped spherical or aspherical surfaces with different curvatures, or a combination of both. However, conventional multifocal IOLs still suffer from the problem of visual discontinuity, which results in obvious visual impairments or breaks between the multiple foci. The visual impairments or breaks cause visual discontinuities, which further reduce the patient's ability to distinguish moving objects.

[0003] Therefore, designing a full-range intraocular lens to provide a patient with continuous vision and improve the patient's dynamic visual acuity is currently a technical problem to be solved by those skilled in the art. Summary of the Invention [Problem to be solved by the invention]

[0004] The present invention provides a full-visibility intraocular lens to solve the problem of visibility discontinuity of diffractive multifocal intraocular lenses, improve the utilization rate of light energy, reduce sharp points on the entire optical surface, effectively reduce glare, reduce chromatic aberration, provide clearer vision in the entire visibility range between foci, and bring patients a better visual experience. [Means for solving the problem]

[0005] The technical solutions of the present invention to achieve the above effects are as follows: A full-visibility intraocular lens including an optical portion, the optical portion being composed of two optical surfaces, the optical surfaces being spherical or aspherical, one of the optical surfaces having a diffractive structure for modulating an optical field distribution of incident light, A method for determining the upper optical surface of the optical part is as follows: A Cartesian coordinate system is established in an arbitrary space with the vertex of the optical surface as the origin O and the optical axis as the Z axis, the X-axis and Y-axis of the coordinate system are tangent to the optical surface, and the surface shape of the optical surface satisfies the following equation in the YZ plane: In the formula, Z(y) is a curve expression of an optical surface in the YZ plane of a two-dimensional coordinate system, c is the inverse of the radius of curvature of the base sphere of the optical surface, y is the perpendicular distance of any point on the curve to the Z axis, and A 2i is a coefficient of a high-order term of the optical surface, m and n are integers of 1 or more and n>m, K is an optical surface coefficient, and K and A 2i When is 0, Z(y) becomes the equation of a sphere, A method for modulating the optical field distribution of incident light by a diffractive structure is as follows: The diffractive structure includes a diffractive ring structure and a discrete diffractive phase point. First, the diffractive ring structure is used to determine a fixed focus. That is, for a single focus diffractive element having a diffractive ring structure, its phase is represented by a diffractive phase function Φ; Φ(x,y)=ρ 1 x 2 +ρ 2 x 4 (2) In the formula, x and y represent the ordinate and abscissa, respectively, in millimeters (mm), and ρ 1 , ρ 2 are the coefficients of each term of the diffraction phase. After compressing the diffraction phase function with a period of 2π, the phase function T(Φ) of the diffraction annulus structure is obtained, T(Φ) = Φ-int(Φ / 2π) × 2π(3) In the formula, int() represents the function that rounds to an integer. Next, discrete diffraction phase points in the sub-wavelength region are introduced. According to Fermat's principle, the propagation path of light is a path where the optical path length has an extreme value, and this extreme value is a maximum value, a minimum value, or an inflection point of a function, which can be expressed by the following formula: TIFF2024545527000003.tif15170TIFF2024545527000004.tif44170TIFF2024545527000005.tif13168TIFF2024545527000006.tif36170

[0006] In the above embodiment, the discrete diffraction phase points in the sub-wavelength region are introduced to modulate the optical field distribution of the incident light, thereby changing the optical path length, and further changing the focal position within a certain range to expand the focal depth range. By introducing multiple discrete diffraction phase points in different sub-wavelength regions into the same diffraction structure region, the focal depth range of the single-focus diffractive element can be expanded from one that focuses on only one focal point to one that can form a continuous and clear image, and two or more focal points can be connected to provide the patient with continuous vision, realizing a jump from point vision to continuous vision, improving the patient's dynamic visual acuity and improving the utilization rate of light energy.

[0007] Furthermore, the optical portion is a biconvex / concave-convex lens having an effective optical portion diameter of 5.5 to 6.5 mm and a center thickness of 0.4 to 1.25 mm.

[0008] Furthermore, the optical section has two or more secondary foci, the secondary foci refractive power ranges from +1.5D to +5D, and the total visibility ranges from +1.5D to +5D.

[0009] The optic may be a trifocal intraocular lens.

[0010] Moreover, the intraocular lens further includes a first haptic and a second haptic, and the optical portion is located between the first haptic and the second haptic.

[0011] Furthermore, the optical portion, the first support portion, and the second support portion are integrally formed from the same material to form an integral structure.

[0012] Furthermore, the first support portion and the second support portion each have a thickness of 0.15 to 0.35 mm.

[0013] Furthermore, the first support portion and the second support portion each have a surface provided with oblique sawtooth recesses or surface roughening projections.

[0014] Furthermore, the width of the oblique sawtooth recesses or surface roughening projections is 0.2 to 1.0 mm.

[0015] Furthermore, the height of the oblique sawtooth recesses or surface roughening projections is greater than 40 μm.

[0016] Furthermore, the angle α that the oblique edge of the oblique sawtooth makes with respect to the plane on which the first support portion and the second support portion are located is −20° to +20°.

[0017] The manufacture of a full visibility intraocular lens involves the following design steps: (1) Optical design, in which the intraocular lens is divided into m+n regions like concentric rings, where m is the number of fixed focus regions (regions where the diffractive annular structure is located), m+1 is the number of foci, and n is the number of continuous regions (regions where the discrete diffractive phase points are located) (for example, when designing a trifocal intraocular lens, if the two foci are connected, the intraocular lens is divided into 3-1+1=3 regions). Among them, the continuous region has the effect of full visibility, the area of ​​the fixed focus region accounts for 50%-70% of the area of ​​the entire diffractive structure, and the area of ​​the continuous region accounts for 30%-50% of the area of ​​the entire diffractive structure.

[0018] The fixed focus area is designed like a conventional bifocal intraocular lens, by first determining the number of secondary foci and their respective focal powers, building an initial model in Zemax, and then optimizing to obtain the best desired effect, obtaining the basic diffraction parameters, and determining the polynomial expression of the diffraction phase function. Φ 1 (x,y)=ρ 11 x 2 +ρ 21 x 4 Φ 2 (x,y)=ρ 12 x 2 +ρ 22 x 4 … Φ m (x,y)=ρ 1m x 2 +ρ 2m x 4 In the formula, m is a positive integer equal to or greater than 2. The surface contours Z of the two optical surfaces of the intraocular lens A and Z B The diffraction phase function is compressed by a period of 2π, and the height h of the diffraction structure corresponding to each radial position x is calculated. 回折 The diffraction ring structure is superimposed on an optical surface in the optical region to obtain the shape Z of the actual optical surface in the fixed focal region. 合成 =Z ベース +h 回折 Get Z ベース is the refractive base surface.

[0019] TIFF2024545527000007.tif35170

[0020] TIFF2024545527000008.tif37170

[0021] (2) Lathe processing of the base refractive lens. According to the processing parameters of the front and rear optical surfaces in the optical design section, a lathe program is prepared, and the optical part is obtained by lathe processing using a single-point cutting technique with diamond. A milling program is prepared, and the shape of the optical area and the roughened surface / serrated leg are obtained by milling.

[0022] (3) A polishing process is performed to obtain an intraocular lens whose optical surface meets the standards.

[0023] The full visibility intraocular lens may be manufactured by obtaining a prototype of the intraocular lens including the diffractive structure by lathe machining, fabricating the optical part of the lens by mechanical engraving, and fabricating the first support part and the second support part by mechanical cutting. Effect of the Invention

[0024] Compared with the prior art, the beneficial effects of the technical solutions of the present invention are as follows: The present invention realizes continuous vision by introducing discrete diffractive phase points into the diffractive structure to extend the focus, so that the patient can not only see clearly at the fixed focus, but also see clearly in the vision between the foci, thus realizing a leap from point vision to continuous vision and solving the problem of discontinuity in vision of diffractive multifocal intraocular lenses.

[0025] The present invention simulates the continuous zoom function of the human eye because the optical area of ​​the optical part has a full-field effect (i.e., continuous field of view), allowing even objects that are constantly moving to be clearly imaged, improving the patient's dynamic visual acuity and allowing moving objects to be clearly imaged.

[0026] The present invention adopts a method of introducing discrete diffractive phase points, and adjusts the optical field distribution of the incident light through a diffractive annular structure to reduce the sharp points on the entire optical surface, effectively reducing glare and chromatic aberration, and bringing patients a better visual experience.

[0027] The present invention does not completely separate the focal points, and the continuous focal depth range improves the utilization rate of light energy to more than 90%, allowing patients to see more clearly in low-light environments.

[0028] The one-piece molded full-vision intraocular lens has a simpler structure than the complex mechanically adjustable intraocular lens, so the intraocular lens of the present invention can adapt to the complex intraocular fluid environment, has good stability, and is less likely to cause secondary cataracts. Furthermore, the roughened / serrated surface design of the support increases the movement resistance of the support, preventing the lens from rotating in the lens capsule, and further improving postoperative stability. [Brief description of the drawings]

[0029] The drawings are merely illustrative and cannot be regarded as limitations on the present invention. In order to better explain the present embodiment, some parts are omitted from the drawings, and the drawings are enlarged or reduced in size, and do not represent the actual dimensions of the products. Even if some known structures and their descriptions are omitted from the drawings, those skilled in the art will understand them. [Figure 1] FIG. 1 is a front and side structural schematic diagram of a full-visibility intraocular lens of Example 1 provided by an embodiment of the present invention. [Diagram 2] FIG. 2 is a front and side structural schematic diagram of a full-visibility intraocular lens of Example 2 provided by an embodiment of the present invention. [Diagram 3] FIG. 3 is a front and side structural schematic diagram of a full-visibility intraocular lens of Example 3 provided by an embodiment of the present invention. [Figure 4] FIG. 4 shows the results of testing the Example 1 provided by the embodiment of the present invention on an eye model with a USAF1951 resolution test chart at different focal powers in a continuous range. [Diagram 5] FIG. 5 shows the results of testing the Example 2 provided by the embodiment of the present invention on an eye model with a USAF1951 resolution test chart at different focal powers in a continuous range. [Figure 6] FIG. 6 shows the results of testing the Example 3 provided by the embodiment of the present invention on an eye model with a USAF1951 resolution test chart at different focal powers in a continuous range. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0030] In order to make the objectives, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions of the embodiments of the present invention will be described clearly and completely below with reference to the drawings of the embodiments of the present invention. Needless to say, the described embodiments are only some of the embodiments of the present invention, and not all of the embodiments. All other embodiments that a person skilled in the art can obtain based on the embodiments of the present invention without inventive work are within the protection scope of the present invention.

[0031] Example 1 This embodiment provides a full-vision intraocular lens including an optical part 1, the optical part 1 being composed of two optical surfaces, the optical surfaces being spherical or aspheric, one of the optical surfaces having a diffractive structure for modulating the optical field distribution of incident light; The method of determining the upper optical surface of the optical portion 1 is as follows: A Cartesian coordinate system is established in an arbitrary space with the vertex of the optical surface as the origin O and the optical axis as the Z axis, the X-axis and Y-axis of the coordinate system are tangent to the optical surface, and the surface shape of the optical surface satisfies the following equation in the YZ plane: In the formula, Z(y) is a curve expression of an optical surface in the YZ plane of a two-dimensional coordinate system, c is the inverse of the radius of curvature of the base sphere of the optical surface, y is the perpendicular distance of any point on the curve to the Z axis, and A 2i is a coefficient of a high-order term of the optical surface, m and n are integers of 1 or more and n>m, K is an optical surface coefficient, and K and A 2i When is 0, Z(y) becomes the equation of a sphere, A method for modulating the optical field distribution of incident light by a diffractive structure is as follows: The diffractive structure includes a diffractive ring structure and a discrete diffractive phase point. First, the diffractive ring structure is used to determine a fixed focus. That is, for a single focus diffractive element having a diffractive ring structure, its phase is represented by a diffractive phase function Φ; Φ(x,y)=ρ 1 x 2 +ρ 2 x 4 (2) In the formula, x and y represent the ordinate and abscissa, respectively, in millimeters (mm), and ρ 1 , ρ 2 are the coefficients of each term of the diffraction phase. After compressing the diffraction phase function with a period of 2π, the phase function T(Φ) of the diffraction annulus structure is obtained, T(Φ) = Φ-int(Φ / 2π) × 2π(3) In the formula, int() represents the function that rounds to an integer. Next, discrete diffraction phase points in the sub-wavelength region are introduced. According to Fermat's principle, the propagation path of light is a path where the optical path length has an extreme value, and this extreme value is a maximum value, a minimum value, or an inflection point of a function, which can be expressed by the following formula: TIFF2024545527000010.tif15170TIFF2024545527000011.tif42169TIFF2024545527000012.tif13168TIFF2024545527000013.tif37170

[0032] Example 2 Specifically, based on Example 1, a specific example is used to explain the technical solution, so as to better express the effect of the technical solution. For ease of understanding, refer to FIG. 1, one embodiment of a full-vision intraocular lens provided by the present invention includes an optical part 1, a first support part 2, and a second support part 3, the optical part 1, the first support part 2, and the second support part 3 are an integral structure integrally molded from the same material, the optical part 1 consists of two optical surfaces (optical surface A and optical surface B), the optical surfaces are spherical or aspherical, among which, optical surface A has a diffractive structure for modulating the optical field distribution of incident light.

[0033] The diffractive structure is embossed by lathe machining on one optical surface of the optical portion 1, where the diffractive structure is superimposed on the optical surface A. The surfaces of the first support portion 2 and the second support portion 3 are both provided with oblique sawtooth recesses, the height of the oblique sawtooth is greater than 40 μm, the width of the oblique sawtooth recess is 0.2 mm, and the angle α of the oblique edge of the oblique sawtooth with respect to the plane on which the support portions are located is 20°. The support portions include the first support portion 2 and the second support portion 3.

[0034] The optical portion 1 is a biconvex lens with an effective optical portion diameter of 6.0 mm and a center thickness of 0.67 mm. The first support portion 2 and the second support portion 3 each have a thickness of 0.15 mm. The optical portion 1 is made of hydrophobic polyacrylate with a refractive index of 1.544 and a dispersion coefficient of 45 to 55.

[0035] The manufacturing method of the full visibility intraocular lens of this embodiment is as follows. (1) Overall design: A trifocal intraocular lens with a distance focus of 20D, an intermediate focus of 2D, and a near focus of 3D is designed, with the intermediate and near focuses being continuous.

[0036] (2) Optical design, in which the fixed focal area and the continuous area are divided by the preset multi-focal focal lengths, i.e., 50mm (20D), 45.45mm (22D), and 43.48mm (23D), where there are two fixed focal areas and one continuous area. The fixed focal area is 70% of the total area, and the continuous area is 30% of the total area. An initial model is constructed in Zemax and optimized to obtain the parameters of optical surface A and optical surface B of optical unit 1, where the base radius is 20.5mm and K=-11.68. The phase functions of the two fixed focal areas are determined based on the phase coefficient. Φ 1 (x,y)=-101.13x 2 -0.986x 4 Φ 2 (x,y)=-151.7x 2 -1.48x 4 Given two consecutive foci 22D and 23D, we decide to add five discrete diffractive phase points uniformly distributed in a continuous area, the size of which is Φ 1 and Φ 2 is the intermediate value.

[0037] (3) Lathe machining of the base refractive lens, in which a lathe program is created according to the parameters of the designed optical region, and a diamond single-point cutting technique is used to obtain a template of the intraocular lens by lathe machining, and a milling program is created to obtain a leg having the shape of the optical region and a roughened surface by milling.

[0038] (4) A polishing process is performed to obtain an intraocular lens whose optical surface meets the standards.

[0039] (5) Analyze and test in eye models.

[0040] The full-range intraocular lens IOL of embodiment 1 is introduced into the eye model specified in ISO11979-2, and is tested by optical equipment to obtain the test results by the USAF1951 resolution test chart at 0.2D intervals between 22D and 23D. As can be seen from Fig. 4, the full-range intraocular lens IOL can obtain clear visual effects between 22D and 23D. In the figure, a is 22D, b is 22.2D, c is 22.4D, d is 22.6D, e is 22.8D, and f is 23D.

[0041] In the prior art, the full-visibility intraocular lens IOL has the disadvantages of insufficient visibility, and obvious visual impairment and even interruptions occur between multiple foci. The visual impairment or interruptions cause discontinuity in visibility, which reduces the patient's ability to distinguish moving objects. In response to this problem, the present invention introduces discrete diffractive phase points to modulate the optical field distribution of the incident light, thereby making two or more foci continuous. When the MTF value was measured using a simulated eye model, all of the values ​​in the continuous range were greater than 0.13, providing the patient with a continuous and clear visual acuity of 0.6 or more. This realizes a leap from point vision to continuous visual acuity, improves the patient's dynamic visual acuity, and allows the patient to clearly image moving objects, improving the patient's quality of life, while also reducing glare, reducing chromatic aberration, and improving the utilization rate of light energy.

[0042] In addition, in the present invention, the optical zone of the optical part 1 is bifocal, trifocal, or multifocal. The present invention has a good improvement effect on the problem that the discontinuity of visibility is relatively obvious in the range from intermediate vision to near vision in trifocal IOL.

[0043] Example 3 Specifically, based on Example 1, a specific example is used to explain the technical solution, so as to better express the effect of the technical solution. A full-visibility intraocular lens includes an optical portion 1, a first support portion 2, and a second support portion 3, the optical portion 1 being composed of an optical surface A, an optical surface B, and a diffractive structure, the diffractive structure being on optical surface A. The optical portion 1, the first support portion 2, and the second support portion 3 are an integral structure integrally molded from the same material, and the diffractive structure is embossed on one optical surface of the optical portion 1 by lathe processing, where the diffractive structure is superimposed on optical surface A.

[0044] Both the surfaces of the first support part 2 and the second support part 3 are provided with several oblique sawtooth recesses, the width of the oblique sawtooth recesses is 0.2 mm, the angle α of the oblique edge of the oblique sawtooth with respect to the plane on which the support parts are located is 20°, and the height of the oblique sawtooth is greater than 40 μm.

[0045] The optical portion 1 is a biconvex lens with an effective optical portion diameter of 5.5 mm and a center thickness of 0.6 mm. The first support portion 2 and the second support portion 3 each have a thickness of 0.15 mm. The optical portion 1 is made of hydrophobic polyacrylate with a refractive index of 1.544 and a dispersion coefficient of 45-55.

[0046] The manufacturing method of the full visibility intraocular lens of this embodiment is as follows. (1) Overall design: A trifocal intraocular lens with a distance focus of 15D, an intermediate focus of 2D, and a near focus of 4D is designed, with the intermediate and near focuses being continuous.

[0047] (2) Optical design, the fixed focal area and the continuous area are divided by the preset multi-focal focal lengths, i.e., 66.67mm (15D), 58.82mm (17D), and 52.63mm (19D), where there are two fixed focal areas and one continuous area. The fixed focal area is 50% of the total area, and the continuous area is 50% of the total area. An initial model is constructed in Zemax and optimized to obtain the parameters of optical surface A and optical surface B of optical unit 1, where the base radius is 31.57mm and K=-19.74. The phase functions of the two fixed focal areas are determined based on the phase coefficient. Φ 1 (x,y)=-101.2x 2 +0.72x 4 Φ 2 (x,y)=-202.22x 2 -1.424x 4 Given two consecutive foci 17D and 19D, we decide to add 10 discrete diffractive phase points uniformly distributed in a continuous area, the size of which is Φ 1 and Φ 2 is the intermediate value.

[0048] (3) Lathe machining of the base refractive lens, in which a lathe program is created according to the parameters of the designed optical region, and a diamond single-point cutting technique is used to obtain a template of the intraocular lens by lathe machining, and a milling program is created to obtain a leg having the shape of the optical region and a roughened surface by milling.

[0049] (4) A polishing process is performed to obtain an intraocular lens whose optical surface meets the standards.

[0050] (5) Analyze and test in eye models.

[0051] The intraocular lens IOL of this embodiment is introduced into the eye model specified by ISO11979-2, and tested with an optical instrument to obtain the test results by the USAF1951 resolution test chart at every 0.2D between the intermediate focus (17D) and the near focus (19D). As can be seen from Figure 5, the full-field intraocular lens IOL can obtain clear visual effects between 17D and 19D. In the figure, a is 17D, b is 17.2D, c is 17.4D, d is 17.6D, e is 17.8D, f is 18D, g is 18.2D, h is 18.4D, i is 18.6D, j is 18.8D, and k is 19D.

[0052] Example 4 Specifically, based on Example 1, a specific example is used to explain the technical solution, so as to better express the effect of the technical solution. As shown in FIG. 3, the full-visibility intraocular lens includes an optical portion 1, a first support portion 2, and a second support portion 3. The optical portion 1 is composed of an optical surface A, an optical surface B, and a diffractive structure, and the diffractive structure is on the optical surface A.

[0053] The optical section 1, the first support section 2, and the second support section 3 are an integral structure integrally molded from the same material, and the diffractive structure is embossed on one optical surface of the optical section 1 by lathe processing, where the diffractive structure is superimposed on optical surface A. Both the surfaces of the first support part 2 and the second support part 3 have several oblique sawtooth-shaped recesses, the height of the oblique sawtooth is greater than 40 μm, the width of the oblique sawtooth-shaped recesses is 0.2 mm, and the angle α of the oblique edge of the oblique sawtooth with respect to the plane on which the support part is located is 20°.

[0054] The optical portion 1 is a biconvex lens with an effective optical portion diameter of 5.5 mm and a center thickness of 0.78 mm. The first support portion 2 and the second support portion 3 each have a thickness of 0.15 mm. The optical portion 1 is made of hydrophobic polyacrylate with a refractive index of 1.544 and a dispersion coefficient of 45-55.

[0055] The manufacturing method of the full visibility intraocular lens of this embodiment is as follows. (1) Overall design: A trifocal intraocular lens with a distance focus of 28D, an intermediate focus of 2.5D, and a near focus of 4D is designed, with the intermediate and near focuses being continuous.

[0056] (2) Optical design, the fixed focal area and the continuous area are divided by the preset multi-focal focal lengths, i.e., 35.71mm (28D), 32.79mm (30.5D), and 31.25mm (32D), where there are two fixed focal areas and one continuous area. The fixed focal area is 60% of the total area, and the continuous area is 40% of the total area. An initial model is constructed in Zemax and optimized to obtain the parameters of optical surface A and optical surface B of optical unit 1, where the base radius is 15.75mm and K=-8.14. The phase functions of the two fixed focal areas are determined based on the phase coefficient. Φ 1 (x,y)=-128.746x 2 +0.096x 4 Φ 2 (x,y)=-206.925x 2 +0.709x 4 Given two consecutive foci 30.5D and 33D, we decide to add eight discrete diffractive phase points uniformly distributed in a continuous area, whose size is Φ 1 and Φ 2 is the intermediate value.

[0057] (3) Lathe machining of the base refractive lens, in which a lathe program is created according to the parameters of the designed optical region, and a diamond single-point cutting technique is used to obtain a template of the intraocular lens by lathe machining, and a milling program is created to obtain a leg having the shape of the optical region and a roughened surface by milling.

[0058] (4) A polishing process is performed to obtain an intraocular lens whose optical surface meets the standards.

[0059] (5) Analyze and test in eye models.

[0060] The intraocular lens IOL of this embodiment is introduced into the eye model specified in ISO11979-2, and tested with an optical instrument to obtain the test results by the USAF1951 resolution test chart at every 0.2D between the intermediate focus (30.5D) and the near focus (32D). As can be seen from Figure 6, clear visual effects can be obtained between 30.5D and 32D. In the figure, a is 30.5D, b is 30.6D, c is 30.8D, d is 31D, e is 31.2D, f is 31.4D, g is 31.6D, h is 31.8D, and i is 32D.

[0061] Although the above examples explain the effects of implementing the present invention using a trifocal intraocular lens as an example, the solution of the present invention to the problem of discontinuity in visibility in diffractive multifocal intraocular lenses also applies to other diffractive multifocal intraocular lenses.

[0062] Needless to say, the above examples of the present invention are merely examples given to clearly explain the present invention, and are not intended to limit the embodiments of the present invention. Those skilled in the art may make various modifications or amendments based on the above description. It is not necessary or possible to list all the embodiments here. Any amendments, equivalent replacements, improvements, etc. made without departing from the spirit and principles of the present invention shall be included within the scope of protection of the claims of the present invention.

Claims

1. A full-visibility intraocular lens including an optical part (1), The optical unit (1) is composed of two optical surfaces, the optical surfaces being spherical or aspherical, one of the optical surfaces having a diffractive structure for modulating the optical field distribution of incident light; A method for determining the upper optical surface of the optical portion (1) is as follows: A Cartesian coordinate system is established in an arbitrary space with the vertex of the optical surface as the origin O and the optical axis as the Z axis, the X-axis and the Y-axis of the coordinate system are tangent to the optical surface, and the surface shape of the optical surface satisfies the following equation in the YZ plane: where Z(y) is a curve expression of the optical surface in the YZ plane of a two-dimensional coordinate system, c is the inverse of the radius of curvature of the base sphere of the optical surface, y is the perpendicular distance of any point on the curve to the Z axis, and A ２ｉ is a coefficient of a high-order term of the optical surface, m and n are both integers of 1 or more and n>m, K is an optical surface coefficient, and K and A ２ｉ When is 0, Z(y) becomes the equation of a sphere, A method for modulating the optical field distribution of incident light by a diffractive structure is as follows: The diffractive structure includes a diffractive ring structure and a discrete diffractive phase point. First, the diffractive ring structure is used to determine a fixed focus. That is, for a single focus diffractive element having a diffractive ring structure, its phase is represented by a diffractive phase function Φ; Φ(x,y)=r １ + ２ +r ２ + ４ (2) In the formula, x and y represent the ordinate and abscissa, respectively, in millimeters (mm), and ρ １ , ρ ２ is the coefficient of each term of the diffraction phase. After compressing the diffraction phase function with a period of 2π, the phase function T(Φ) of the diffraction annulus structure is obtained, T(Φ)=Φ-int(Φ / 2π)×2π(3) In the formula, int() represents the integer rounding function, Next, discrete diffraction phase points in the sub-wavelength region are introduced. According to Fermat's principle, the propagation path of light is a path where the optical path length has an extreme value, and this extreme value is a maximum value, a minimum value, or an inflection point of a function, which can be expressed by the following formula:

2. The full-visibility intraocular lens according to claim 1, characterized in that the optical portion (1) is a biconvex / concave-convex lens having an effective optical portion diameter of 5.5 to 6.5 mm and a center thickness of 0.4 to 1.25 mm.

3. A full-visibility intraocular lens according to claim 1, characterized in that the optical part (1) has two or more secondary foci.

4. The full-visibility intraocular lens according to claim 1, characterized in that the intraocular lens further comprises a first support portion (2) and a second support portion (3), and the optical portion (1) is located between the first support portion (2) and the second support portion (3).

5. The full-visibility intraocular lens according to claim 4, characterized in that the optical portion (1), the first support portion (2), and the second support portion (3) are integrally molded from the same material to form an integrated structure.

6. 5. The full-visibility intraocular lens according to claim 4, wherein the thickness of each of the first support portion (2) and the second support portion (3) is 0.15 to 0.35 mm.

7. The full-visibility intraocular lens according to any one of claims 4 to 6, characterized in that the surfaces of both the first support portion (2) and the second support portion (3) are provided with oblique sawtooth-shaped recesses or surface roughening protrusions.

8. The full visibility intraocular lens according to claim 7, characterized in that the width of the oblique sawtooth recesses or surface roughening projections is 0.2 to 1.0 mm.

9. The full-visibility intraocular lens according to claim 8 , wherein the height of the oblique sawtooth recesses or surface roughening protrusions is greater than 40 μm.

10. The full-visibility intraocular lens according to claim 9, characterized in that the angle α of the oblique edge of the oblique sawtooth with respect to the plane on which the first support portion (2) and the second support portion (3) are located is between -20° and +20°.

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