Focal depth lengthening intraocular lens based on sinusoidal grating
By setting a sinusoidal grating on the artificial lens, stable and continuous imaging within the focal depth range is achieved, solving the problems of light energy loss and poor imaging in existing EDOF IOLs, and improving visual adaptability and structural stability.
Patent Information
- Application Number
- CN202511540689.1
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- Filing Date
- 2025-10-27
- Publication Date
- 2025-12-26
Smart Images
Figure CN121196799A_ABST
Abstract
Description
Technical Field
[0001] This invention belongs to the field of intraocular lens technology, and more specifically, relates to an intraocular lens with extended focal depth based on a sinusoidal grating. Background Technology
[0002] Intraocular lenses (IOLs) are widely used in cataract surgery to replace the diseased natural lens in patients' eyes. IOLs can be classified according to the number of focal points and imaging results, including monofocal IOLs, bifocal IOLs, trifocal IOLs, and extended depth of focus (EDOF) IOLs. While monofocal IOLs currently dominate the market, with the development of intraocular lenses and societal progress, EDOF IOLs, as a substitute for monofocal IOLs, are expected to gradually increase their market share.
[0003] The main principles of current EDOF IOLs on the market are: depth of focus extension achieved through multiple focal points or modulation of spherical aberration. The depth of focus extension achieved through multiple focal points, mainly through refraction and diffraction, results in some light energy loss and poor continuity within the focal depth range, exhibiting strong optical interference. Similarly, depth of focus extension achieved through modulation of spherical aberration is prone to optical interference such as aperture rings, leading to unsatisfactory image clarity within the focal depth range. Existing technologies also utilize a phase grating set in the central region to extend the focal depth, adjusting the phase and period of the incident light to achieve phase changes in the image. However, this structure results in diffraction rings becoming denser closer to the lens edge. This periodic variation and structural design respond to the light energy distribution of additional focal points and optical power, thus affecting the length of the focal depth range and the resulting sharpness. To address these issues, this patent proposes a depth-of-focus extension IOL based on a sinusoidal grating, which enables continuous and clear imaging within the focal depth range, reducing light energy loss and improving postoperative visual adaptation for patients. Summary of the Invention
[0004] The purpose of this invention is to solve the above-mentioned technical problems and provide an intraocular lens with extended focal depth based on a sinusoidal grating, which can provide continuous and clear imaging within the focal depth range, reduce light energy loss and improve the patient's postoperative visual adaptation.
[0005] To achieve the above objectives, the present invention adopts the following technical solution: This invention provides an intraocular lens with extended focal depth, comprising an optical body, an optical surface on which an optical region is provided, the optical surface being provided with a central region, a grating region and an edge region from the inside out, light waves from a light source passing through the central region and the edge region to form a fundamental light function; the grating region is provided with a sinusoidal amplitude grating for forming multiple harmonics, the fundamental light function and the multiple harmonic light functions interfering at the same position; The structure function of the sinusoidal amplitude grating is shown in equation (Ⅲ): (III) Where h is the amplitude coefficient, d is the wavelength of the light source; d is the spatial frequency. The fundamental wave optical function formed by the central region and the edge region is shown in equation (Ⅳ): (IV) Where k is the frequency, f1 is the posterior focal length of the intraocular lens, and i represents an imaginary number; The optical function that generates multiple harmonics after passing through a sinusoidal amplitude grating is shown in equation (V): (V) The fundamental light function formed by the light wave passing through the central and edge regions and the multiple harmonic light function formed after passing through the sinusoidal amplitude grating interfere at the same position, satisfying equation (VI): (VI) The above function coordinate system satisfies the following: an arbitrary spatial rectangular coordinate system is established with the vertex of the optical surface as the origin O and the optical axis as the Z-axis, and the x-axis and y-axis of the coordinate system are tangent to the optical surface. The multiple harmonics refer to the third harmonic and above.
[0006] Furthermore, the optical surfaces are disposed on both sides of the optical body, and the grating area is disposed on the optical surface on one side or both sides of the optical body. The optical surfaces are spherical or aspherical; their surface shape satisfies the equation shown in equation (Ⅰ) on the YZ plane: (I) Where Z(y) is the curve expression, c is the reciprocal of the radius of curvature of the aspherical surface or the basic spherical surface, y is the vertical distance from any point on the curve to the horizontal coordinate axis Z, and A 2i are the coefficients of higher-order terms of aspherical surfaces, where m and n are integers not less than 1 and n > m, and K is the coefficient of aspherical surface.
[0007] Furthermore, a support haptic is connected to the outer side of the optical body. The support haptic is a C-shaped haptic, an L-shaped haptic, or a flat haptic, and the support haptic and the optical body are an integral structure.
[0008] Furthermore, the support loop is provided with oblique sawtooth grooves or raised frosted surfaces; the roughness of the frosted surface or the height of the oblique sawtooth is greater than 40 μm; the width of the oblique sawtooth grooves or raised frosted surfaces is 0.2 to 1.0 mm, and the angle α between the oblique edge of the oblique sawtooth and the support loop is -20° to 20°; the thickness of the support loop is 0.15 to 0.45 mm. Further, the refractive index of the optical body is 1.45~1.60, and the dispersion coefficient of the optical body is 35~65; preferably, the refractive index of the optical body is 1.544, and the dispersion coefficient of the optical body is 45~55.
[0009] Preferably, the optical body is made of a material such as hydrophobic polyacrylate, hydrophilic polyacrylate, or PMMA; more preferably, the optical body is made of hydrophobic polyacrylate.
[0010] Furthermore, the transmission function of the sinusoidal amplitude grating satisfies equation (II): (II) Where d is the spatial frequency of the grating.
[0011] Furthermore, the diameter of the optical body is 5.0–6.5 mm, and the center thickness is 0.2–1.25 mm.
[0012] Furthermore, the grating area is annular, with an outer radius of 0.8 mm to 1.5 mm and an inner radius of 0.3 mm to 1.0 mm.
[0013] Furthermore, the optical power of the optical body is -40 D to 40 D.
[0014] Preferably, the lens shape of the optical body is biconvex, plano-convex, concave-convex, biconcave, or plano-concave.
[0015] Furthermore, the amplitude coefficient h of the sinusoidal amplitude grating is 1~10, and the spatial frequency d is 0~1.
[0016] The beneficial effects of this invention are as follows: (1) The present invention extends the focal depth by superimposing a sinusoidal amplitude grating on the optical surface of the artificial lens, and by interfering the fundamental wave in the central region and the edge region to generate multiple harmonics coherent with the light wave of the light source. Finally, the two are interfered to form a stable and continuous steady-state harmonic, thereby achieving the purpose of extending the focal depth.
[0017] (2) The depth-of-focus intraocular lens of the present invention can provide continuous and clear imaging within the depth of focus range, reduce light energy loss and improve the patient's postoperative visual adaptation, and enrich the product range of depth-of-focus intraocular lenses.
[0018] (3) Compared with complex mechanically adjustable intraocular lenses, the depth-of-focus artificial lens of the present invention has a simple structure, which makes the lens suitable for complex ocular fluid environment, has good stability, and is less likely to induce grade II cataracts. Attached Figure Description
[0019] Figure 1 The optical body and support haptic structure of the depth-of-focus extended intraocular lens of the present invention are shown in Figure A, which is a front view and B is a side view. In the figure, 100 represents the optical body, 200 represents the support haptic, 111 represents the central region, 112 represents the grating region, and 113 represents the edge region.
[0020] Figure 2 Wavefront plot of the fundamental wave function; The horizontal axis in the graph represents the normalized diameter (without units), and the vertical axis represents the amplitude height (in mm).
[0021] Figure 3 This is a wavefront diagram of the optical function of multiple harmonics formed after parallel light passes through a sinusoidal amplitude grating in Example 2. In the figure, the horizontal axis represents the normalized diameter (without units), the vertical axis represents the amplitude height (in mm), and d is the grating spatial frequency.
[0022] Figure 4 The wavefront diagram of Example 2 shows the interference between the fundamental wave function formed by the light wave from the light source passing through the central and edge regions and the multiple harmonic wave function formed after passing through the sinusoidal amplitude grating at the same location. In the figure, the horizontal axis represents the normalized diameter (without units), and the vertical axis represents the amplitude height (in mm). The bold line represents the waveform after interference, the solid line represents the fundamental waveform, and the dashed line represents the third harmonic waveform.
[0023] Figure 5 The wavefront diagram of the optical function that forms multiple harmonics after parallel light passes through a sinusoidal amplitude grating in Example 3; In the figure, the horizontal axis represents the normalized diameter (without units), the vertical axis represents the amplitude height (in mm), and d is the grating spatial frequency.
[0024] Figure 6 The wavefront diagram of Example 3 shows the interference between the fundamental wave function formed by the light wave from the light source passing through the central and edge regions and the multiple harmonic wave function formed after passing through the sinusoidal amplitude grating at the same location. In the figure, the horizontal axis represents the normalized diameter (without units), and the vertical axis represents the amplitude height (in mm). The bold line represents the waveform after interference, the solid line represents the fundamental waveform, and the dashed line represents the third harmonic waveform.
[0025] Figure 7 This is a test image of the USAF1951 artificial lens resolution board from Example 2.
[0026] Figure 8This is a test image of the USAF1951 artificial lens resolution board from Example 3. Detailed Implementation
[0027] To enable those skilled in the art to better understand the present invention, the technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort should fall within the scope of protection of the present invention.
[0028] Example 1 This embodiment provides an intraocular lens with extended focal depth, such as... Figure 1 As shown, it includes an optical body 100, on which an optical surface 110 is provided. The optical surface is provided with a central region 111, a grating region 112 and an edge region 113 from the inside to the outside. The light wave of the light source passes through the central region 111 and the edge region 113 to form the fundamental light function. The grating region 112 is provided with a sinusoidal amplitude grating for forming multiple harmonics. The fundamental light function and the multiple harmonic light functions interfere at the same position.
[0029] Alternatively, the optical surfaces are disposed on both sides of the optical body, and the grating area is disposed on one or both optical surfaces of the optical body. The optical surfaces are spherical or aspherical; their surface shape satisfies the following equation in the YZ plane: (I) Where Z(y) is the curve expression, c is the reciprocal of the radius of curvature of the aspherical surface or the basic spherical surface, y is the vertical distance of any point on the curve from the horizontal coordinate axis Z, and A 2i Let K be the coefficient of the aspherical higher-order term, where m and n are both integers not less than 1 and n > m, and K is the aspherical coefficient; when K and A 2i When the value is 0, Z(y) is the equation of the sphere.
[0030] As an alternative, the transmission function of the sinusoidal amplitude grating is expressed as: (II) Where d is the spatial frequency of the grating.
[0031] Alternatively, a support loop is connected to the outer side of the optical body. The support loop can be a C-shaped loop, an L-shaped loop, or a flat loop, and the support loop and the optical body are an integral structure. Preferably, the support loop has oblique serrated grooves or raised frosted surfaces; the roughness of the frosted surface or the height of the oblique serrations is greater than 40 μm; the width of the oblique serrated grooves or raised frosted surfaces is 0.2 to 1.0 mm, the angle α between the oblique edge of the oblique serrations and the support loop is -20° to 20°, and the thickness of the support loop is 0.15 to 0.45 mm. Alternatively, the refractive index of the optical body is 1.45~1.60, and the dispersion coefficient of the optical body is 35~65; preferably, the refractive index of the optical body is 1.544, and the dispersion coefficient of the optical body is 45~55.
[0032] Preferably, the optical body is made of materials such as hydrophobic polyacrylate, hydrophilic polyacrylate, or PMMA; more preferably, the optical body is made of hydrophobic polyacrylate.
[0033] As an alternative, the diameter of the optical body is 5.0–6.5 mm and the center thickness is 0.2–1.25 mm.
[0034] As an alternative, the grating area is annular, with an outer radius of 0.8 mm to 1.5 mm and an inner radius of 0.3 mm to 1.0 mm.
[0035] As an alternative, the optical power of the main optical unit is -40 D to 40 D.
[0036] Alternatively, the lens shape of the optical body can be biconvex, plano-convex, concave-convex, biconcave, or plano-concave.
[0037] As an alternative, the amplitude coefficient h of the sinusoidal amplitude grating is 1~10, and the spatial frequency d is 0~1.
[0038] As an alternative, the structure function of the sinusoidal amplitude grating is shown in equation (Ⅲ): (III) Where h is the amplitude coefficient, d is the wavelength of the light source; d is the spatial frequency. The fundamental wave light function formed by parallel light passing through the central and edge regions is shown in equation (Ⅳ): (IV) Where k is the frequency, f1 is the posterior focal length of the intraocular lens, and i represents an imaginary number; like Figure 2 As can be seen, the wavefront plot of the fundamental optical function has the horizontal axis as the normalized diameter and the vertical axis as the wavefront amplitude. The wavefront plot shows that the focusing effect is determined after the top focal length of the intraocular lens is determined.
[0039] The optical function of the third harmonic formed after parallel light passes through a sinusoidal amplitude grating is shown in equation (V): (V) Different spatial frequencies produce different third harmonics.
[0040] The fundamental light function formed by the light wave passing through the central and edge regions and the third harmonic light function formed after passing through the sinusoidal amplitude grating interfere at the same position, satisfying equation (VI): (VI) The above function coordinate system satisfies the following: with the vertex of the optical surface as the origin O and the optical axis as the Z-axis, an arbitrary spatial rectangular coordinate system is established, and the x-axis and y-axis of the coordinate system are tangent to the optical surface.
[0041] The depth of focus is determined by the amplitude height of the wavefront after interference and the focusing effect, and is related to the amplitude coefficient h and the spatial frequency d. Choosing appropriate amplitude coefficient h and spatial frequency d can extend the depth of focus of the intraocular lens, and continuous and clear imaging can be achieved within the depth of focus range.
[0042] Example 2 This embodiment provides an intraocular lens with extended focal depth, such as... Figure 1 As shown, it includes an optical body 100 and a support haptic 200. The optical body 100 is provided with an optical surface 110, which is composed of optical surfaces A and B. An annular sinusoidal amplitude grating is disposed on optical surface A. Optical surface A is provided with a central region 111, a grating region 112 and an edge region 113 from the inside to the outside. The light wave of the light source passes through the central region 111 and the edge region 113 to form the fundamental light function. The annular sinusoidal amplitude grating is disposed in the grating region 112. The fundamental light function and the light functions of multiple harmonics interfere at the same position.
[0043] Preferably, the optical host is made of hydrophobic polyacrylate with a refractive index of 1.544 and a dispersion coefficient of 45 to 55.
[0044] The optical body is a biconvex lens with a diameter of 6 mm and a center thickness of 0.62 mm. Preferably, the grating area is annular, with an outer radius of 1.0 mm and an inner radius of 0.5 mm. Preferably, the optical power of the optical body is 18 D. Alternatively, the amplitude coefficient h of the sinusoidal amplitude grating is 2.5, and the spatial frequency d is 1 / 3.
[0045] Preferably, the support loop is connected to the outside of the optical body, and the optical body and the support loop are an integral structure made of the same material and integrally formed; the support loop is a C-shaped loop. Preferably, the support loop has oblique serrated grooves; the height of the frosted oblique serrations is 80 μm; the width of the oblique serrated groove is 0.13 mm; the angle α between the oblique edge of the oblique serration and the plane to which the support loop belongs is 15°; the thickness of the support loop is 0.40 mm.
[0046] As an alternative, the optical surface is aspherical; its surface shape in the YZ plane satisfies the equation shown in equation (Ⅰ): (I) Where Z(y) is the curve expression, c is the reciprocal of the radius of curvature of the aspherical surface or the basic spherical surface, y is the vertical distance of any point on the curve from the horizontal coordinate axis Z, and A 2i Let K be the coefficient of the aspherical higher-order term, where m and n are both integers not less than 1 and n > m, and K is the aspherical coefficient; when K and A 2i When the value is 0, Z(y) is the equation of the sphere.
[0047] As an alternative, the transmission function of the sinusoidal amplitude grating satisfies equation (II): (II) Where d is the spatial frequency of the grating.
[0048] As an alternative, the structure function of the sinusoidal amplitude grating is shown in equation (Ⅲ): (III) Where h is the amplitude coefficient, λ is the wavelength of the light source; d is the spatial frequency.
[0049] The fundamental wave light function formed by parallel light passing through the central and edge regions is shown in equation (Ⅳ): (IV) Where k is the frequency, f1 is the posterior focal length of the intraocular lens, and i represents an imaginary number; The optical function of the third harmonic formed after parallel light passes through a sinusoidal amplitude grating is shown in equation (V): (V) Wavefront diagrams of the fundamental and third harmonic waves are as follows: Figure 3 As shown.
[0050] The fundamental light function formed by the light wave passing through the central and edge regions and the third harmonic light function formed after passing through the sinusoidal amplitude grating interfere at the same position, satisfying equation (VI): (VI) The above function coordinate system satisfies the following: with the vertex of the optical surface as the origin O and the optical axis as the Z-axis, an arbitrary spatial rectangular coordinate system is established, and the x-axis and y-axis of the coordinate system are tangent to the optical surface.
[0051] Its wavefront diagram is as follows Figure 4 As shown, it can be seen that the wavefront amplitude and focusing degree after interference are better than those of the fundamental wave before interference, and the crystal focal depth extension range is effectively extended.
[0052] The preparation method of the above-mentioned intraocular lens is as follows: Optical design: Based on the optical power of the artificial crystal and the additional optical power, an initial model was constructed in Zemax, and the parameters of the two optical surfaces A and B of the optical body 1 were optimized, where the base radius is 23.56 mm, K = -2.38, and there are no higher-order terms; According to formula (I), the optical surface is aspherical; its surface shape on the YZ plane satisfies the following equation:
[0053] Based on the large radius R = 1 mm and the small radius r = 0.5 mm, the central region, grating region, and edge region are divided to determine the range of the sinusoidal amplitude grating; based on the spatial frequency d = 1 / 3, the transmission function of the sinusoidal amplitude grating is as follows according to formula (II):
[0054] The amplitude coefficient h = 2.5, and the dominant wavelength is 0.546. According to formula (Ⅲ), the sinusoidal amplitude grating structure function for:
[0055] Superimposed on the substrate, the actual surface shape and processing curve Z of the optical surface are obtained. 合 for:
[0056] Machining the substrate refractive lens: A lathe program is written according to the designed optical zone parameters; a circular intraocular lens is machined using diamond single-point cutting technology; a milling program is written to mill the shape of the optical zone and the frosted haptic. Finally, polishing is performed to obtain an intraocular lens with a qualified optical surface.
[0057] An intraocular lens was inserted into an eye model as required by ISO 11979-2, and USAF 1951 resolution plate test images were obtained using optical equipment at 0.5 D intervals from 18 D to 21 D. Figure 5 As shown, this artificial lens has a 2D depth of focus range, within which the image is clear and continuous with minimal optical interference.
[0058] Example 3 like Figure 1 As shown, this embodiment provides a depth-of-focus intraocular lens, which differs from Embodiment 2 in that the annular sinusoidal amplitude grating is on optical surface B, and the relevant parameters of the support haptic and optical body are different, as detailed below: The optical body is a biconvex lens with a diameter of 5.5 mm and a center thickness of 0.69 mm. Preferably, the grating area is annular with an outer radius of 1.2 mm and an inner radius of 0.6 mm. Preferably, the optical power of the optical body is 22 D. Alternatively, the lens shape of the optical body is biconvex. Preferably, the amplitude coefficient h of the sinusoidal amplitude grating is 3.5, and the spatial frequency d is 1 / 5.
[0059] Preferably, the support loop is connected to the outside of the optical body, and the optical body and the support loop are an integral structure made of the same material and molded as a whole; the support loop is a C-shaped loop. Preferably, the support loop has oblique serrated grooves; the height of the frosted oblique serrations is 60 μm; the width of the oblique serrated groove is 0.13 mm; the angle α between the oblique edge of the oblique serration and the plane to which the support loop belongs is 20°; the thickness of the support loop is 0.35 mm.
[0060] The preparation method of the above-mentioned intraocular lens is as follows: Optical design: Based on the crystal power and additional power, an initial model was constructed in Zemax, and the parameters of the two optical surfaces A and B of the optical body 1 were optimized, where the base radius is 19.12 mm, K = -1.98, and there are no higher-order terms; According to formula (I), the optical surface is aspherical; its surface shape satisfies the following equation on the YZ plane:
[0061] Based on the large radius R = 1.2 mm and the small radius r = 0.6 mm, the area is divided into a central region, a grating region, and an edge region to determine the range of the sinusoidal amplitude grating; based on the spatial frequency d = 1 / 5, according to formula (II), the transmission function of the sinusoidal amplitude grating is:
[0062] The amplitude coefficient h = 3.5, and the dominant wavelength is 0.546. And formula (III) Based on formula (III), the sinusoidal amplitude grating structure function for:
[0063] Superimposed on the substrate, the actual surface shape and processing curve Z of the optical surface are obtained. 合 for:
[0064] Machining the substrate refractive lens: A lathe program is written according to the designed optical zone parameters; a circular intraocular lens is machined using diamond single-point cutting technology; a milling program is written to mill the shape of the optical zone and the frosted haptic. Finally, polishing is performed to obtain an intraocular lens with a qualified optical surface.
[0065] An intraocular lens was inserted into an eye model as required by ISO 11979-2, and USAF 1951 resolution plate test images were obtained using optical equipment at 0.5 D intervals from 22 D to 24 D. Figure 6 As shown, this intraocular lens has a focal depth range of 1.5 D, within which the image is clear and continuous with minimal optical interference.
[0066] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and not to limit the solutions. Although the present invention has been described in detail with reference to preferred embodiments, those skilled in the art should understand that modifications or equivalent substitutions can be made to the technical solutions of the present invention based on the understanding of the present invention, without departing from the spirit and scope of the technical solutions of the present invention, and all such modifications or substitutions should be covered within the scope of the claims of the present invention.
Claims
1. A depth-of-focus intraocular lens, characterized in that, The system includes an optical body with an optical surface. The optical surface is provided with a central region, a grating region, and an edge region from the inside out. Light waves from the light source pass through the central region and the edge region to form a fundamental light function. The grating region is provided with a sinusoidal amplitude grating for forming multiple harmonics. The fundamental light function and the multiple harmonic light functions interfere at the same position. The structure function of the sinusoidal amplitude grating is shown in equation (Ⅲ): （Ⅲ） Where h is the amplitude coefficient, d is the wavelength of the light source; d is the spatial frequency. The fundamental light function formed by the light wave passing through the central and edge regions is shown in equation (Ⅳ): （Ⅳ） Where k is the frequency, f1 is the posterior focal length of the intraocular lens, and i represents an imaginary number; The light wave from the light source, after passing through a sinusoidal amplitude grating, forms a light function with multiple harmonics, as shown in equation (V): （Ⅴ） The fundamental light function formed by the light wave passing through the central and edge regions and the multiple harmonic light function formed after passing through the sinusoidal amplitude grating interfere at the same position, satisfying equation (VI): （Ⅵ） The above function coordinate system satisfies the following: an arbitrary spatial rectangular coordinate system is established with the vertex of the optical surface as the origin O and the optical axis as the Z-axis, and the x-axis and y-axis of the coordinate system are tangent to the optical surface. The multiple harmonics refer to the third harmonic and above.
2. The depth-of-focus intraocular lens according to claim 1, characterized in that, The optical surfaces are disposed on both sides of the optical body, and the grating area is disposed on the optical surface on one side or both sides of the optical body. The optical surfaces are spherical or aspherical; their surface shapes satisfy the equation shown in equation (Ⅰ) on the YZ plane: （Ⅰ） Where Z(y) is the curve expression, c is the reciprocal of the radius of curvature of the aspherical surface or the basic spherical surface, y is the vertical distance from any point on the curve to the horizontal coordinate axis Z, and A 2i are the coefficients of higher-order terms of aspherical surfaces, where m and n are integers not less than 1 and n > m, and K is the coefficient of aspherical surface.
3. The depth-of-focus intraocular lens according to claim 1, characterized in that, The optical body is connected to a support haptic on its outer side. The support haptic is a C-shaped haptic, an L-shaped haptic, or a flat haptic. The support haptic and the optical body are an integral structure.
4. The depth-of-focus intraocular lens according to claim 3, characterized in that, The support loop is provided with oblique sawtooth grooves or raised abrasive surfaces; the roughness of the abrasive surface or the height of the oblique sawtooth is greater than 40 μm; the width of the oblique sawtooth grooves or raised abrasive surfaces is 0.2 to 1.0 mm, and the angle α between the oblique edge of the oblique sawtooth and the support loop is -20° to 20°; the thickness of the support loop is 0.15 to 0.45 mm.
5. The depth-of-focus intraocular lens according to claim 1, characterized in that, The optical body has a refractive index of 1.45 to 1.60 and a dispersion coefficient of 35 to 65; preferably, the optical body has a refractive index of 1.544 and a dispersion coefficient of 45 to 55.
6. The depth-of-focus intraocular lens according to claim 1, characterized in that, The transmission function of the sinusoidal amplitude grating satisfies equation (II): （Ⅱ） Where d is the spatial frequency of the grating.
7. The depth-of-focus intraocular lens according to claim 1, characterized in that, The diameter of the optical body is 5.0–6.5 mm, and the center thickness is 0.2–1.25 mm.
8. The depth-of-focus intraocular lens according to claim 1, characterized in that, The grating area is annular, with an outer radius of 0.8 mm to 1.5 mm and an inner radius of 0.3 mm to 1.0 mm.
9. The depth-of-focus intraocular lens according to claim 1, characterized in that, The optical power of the optical body is -40 D to 40 D; preferably, the lens shape of the optical body is biconvex, plano-convex, concave-convex, biconcave, or plano-concave.
10. The depth-of-focus intraocular lens according to claim 1, characterized in that, The amplitude coefficient h of the sinusoidal amplitude grating is 1~10, and the spatial frequency d is 0~1.