Intraocular lens for posterior chamber of eye with extended depth of focus and method for manufacturing the same

Abstract

The present invention discloses a focal depth extending phakic posterior chamber intraocular lens and its manufacturing method, the focal depth extending phakic posterior chamber intraocular lens including an optical part, a first haptic part and a second haptic part, the optical part, the first haptic part and the second haptic part are integrally molded with the same material, the optical part is located between the first haptic part and the second haptic part, the optical part is composed of two optical surfaces, one optical surface is a plane, and the other optical surface is a free-form surface with focal depth extending function. The present invention uses focal depth extending technology in the phakic intraocular lens by introducing a free-form surface, which extends focal depth, corrects myopia and provides a certain degree of accommodation at the same time, the surface is smooth and has no abrupt changes, does not cause glare and halo, corrects the patient's myopia and corrects presbyopia at the same time, and has a good visual effect.

Description

Technical Field

[0001] The present invention relates to the technical field of optical devices, and particularly to an intraocular lens with extended depth of focus for the posterior chamber of the eye with a crystalline lens and a method for manufacturing the same.

Background Art

[0002] An intraocular lens for the posterior chamber of the eye with a crystalline lens is an implantable intraocular lens (ICL) placed in the posterior chamber.

[0003] Due to factors such as bad eye usage habits like long-term use of electronic devices and a decrease in outdoor activities, the eyes are used at close range for a long time, the eye axis is abnormally extended, and refractive abnormalities occur. With the development of technology and the improvement of the demand for vision, many corrective measures have been developed to restore the visual ability of patients. Compared with corrective methods such as therapeutic laser keratectomy, conventional frame glasses, and contact lenses, intraocular lenses for eyes with a crystalline lens have advantages such as not damaging the cornea, not requiring attachment and detachment, and being able to be removed and replaced, so they are increasingly used by many young patients.

[0004] However, as myopic patients age, the accommodation ability of the ciliary muscle weakens, presbyopia problems occur, and patients will have both myopia and presbyopia. As conventional products or methods for correcting refractive abnormalities such as myopia, presbyopia, and astigmatism, for example, frame glasses, contact lenses, therapeutic laser keratectomy, ICL implantation, etc. cannot correct myopia and presbyopia simultaneously.

[0005] Therefore, designing an intraocular lens for eyes with a crystalline lens that can solve the problems of myopia and presbyopia simultaneously and improving the visual quality of patients is a technical problem that those skilled in the art should solve.

Summary of the Invention

Problems to be Solved by the Invention

[0006] The present invention provides an extended depth of focus intraocular lens with the ability to extend and adjust the depth of focus, which can simultaneously solve the problems of myopia and presbyopia, and a method for manufacturing the same.

Means for Solving the Problems

[0007] The technical solution of the present invention for realizing the above effects is as follows. An extended depth of focus intraocular lens including an optical part, a first support part, and a second support part, wherein the optical part, the first support part, and the second support part are of an integrated structure integrally formed of the same material, the optical part is located between the first support part and the second support part, the optical part consists of two optical surfaces, one optical surface is a plane, and the other optical surface is a free surface having an extended depth of focus function.

[0008] Furthermore, one optical surface of the optical part satisfies the design principle of the free surface, and its determination method is as follows. With the vertex of the optical surface as the origin O and the optical axis as the Z axis, an arbitrary orthogonal coordinate system in space is established, and the X axis and Y axis of the coordinate system are tangent to the free surface.

[0009] Furthermore, the design process of the free surface is as follows. By the geometric iteration method, the free surface is divided into a series of partial surfaces to discretize the free surface, and the discretized free surface is represented by the envelope surface of a series of partial surfaces. Since the free surface is rotationally symmetric, here only the partial surface on one meridian is considered as the representative of all partial surfaces. One partial surface A0 on the free surface is known, and its incident light vector and normal vector TIFF0007714809000001.tif145170

[0010] In the above embodiment, the intraocular lens of the present invention has multiple focal points and a long depth of focus range.

[0011] TIFF0007714809000002.tif16170

[0012] Furthermore, the range of the effective optical diameter of the optical part is 4 mm to 6 mm.

[0013] Furthermore, the focal length f0 of the optical part is determined by the focal refractive power of the optical part, and the range of the focal refractive power is 0 D to -30 D.

[0014] Furthermore, the optical part is made of hydrophilic polyacrylate.

[0015] Furthermore, the refractive index of the optical part at 35 °C is 1.437.

[0016] Furthermore, the thicknesses of both the first support part and the second support part are 0.08 mm to 0.15 mm.

[0017] A method for manufacturing an intraocular lens with an extended depth of focus in the posterior chamber of the eye, comprising the following steps for designing the above intraocular lens with an extended depth of focus in the posterior chamber of the eye, S1: Optical design, which determines the focal refractive power, the effective optical diameter, and the extended depth of focus value of the optical part, models them in zemax, uses the free-form surface before discretization as the basic spherical surface, and optimizes to obtain the curvature r of the basic spherical surface that satisfies the focal refractive power requirement of the optical part, and calculates the focal length range f 最小 ~f 最大 of the optical part, f 最小 = 1 / φ f 最大 = 1 / (φ + φ 拡張 )(5) In the formula, f 最小 , f 最大 are respectively the minimum focal length and the maximum focal length of the optical part (1), and φ, φ 拡張 are respectively the focal refractive power and the extended focal refractive power of the optical part (1), Set the number of geometric iterations as i, discretize the basic spherical surface obtained by optimization. Since the intraocular lens is rotationally symmetric, the number of partial surfaces A0 on one meridian will be i. Calculate the positions of the center points of all partial surfaces A0, and use A i to represent any partial surface on one meridian, and (y i , z i) represents the position of the center point of any partial surface A0, and f i represents the focal length of any partial surface A i , and the focal length range f1~f i is divided. Here, the absolute value gradually increases from f1 to f i to prevent interference by the incident light rays, take into account the constriction and dilation of the pupil, and reduce the dependence on the pupil. Therefore, from the center to the outside, the focal length f i of the partial surface A i gradually increases in absolute value, modeling is performed by the geometric iteration method in matlab, and the focal length f i of the partial surface A i and the position of the center point of the partial surface A i (y i , z i ) are used to obtain the angle θ i formed by the outgoing light ray of the partial surface A i with respect to the optical axis, TIFF0007714809000003.tif28170S2: It is a turning process. Based on the free surface designed in step S1, a lathe program for a hydrophilic material is created. Using the single-point cutting technology with diamond, an optical part is obtained by turning, a milling machine program is created, and the shape of the optical region of the optical part and the legs of the first support part and the second support part are obtained by milling, S3: It is a polishing process. The intraocular lens is polished using a low-temperature cylinder, S4: It is verification by testing. The intraocular lens is analyzed and tested in a simulated eye system.

[0018] Note that the normal vector of the partial surface is perpendicular to the tangent plane of the partial surface passing through the partial surface. If the partial surface is a minute spherical surface, the partial surface can be obtained based on the geometric relationship of the normal vector of the partial surface. In step 1, the curvature r of the basic spherical surface that satisfies the focal refractive power requirement of the optical part is obtained through optimization, and the optimization is performed by adjusting the parameters of the basic spherical surface in zemax.

[0019] However, the focal length corresponding to the partial surface A1 is f1, and the focal length corresponding to the partial surface A i is fi It is as follows.

Advantages of the Invention

[0020] Compared with the prior art, the beneficial effects of the technical solution of the present invention are as follows. The present invention uses the depth-of-focus extension technology for the intraocular lens with a crystalline lens, not only for correcting myopia, but also adding the ability to adjust the depth of focus to the lens.

[0021] 1. By introducing a free-form surface, the present invention uses the depth-of-focus extension technology for the intraocular lens with a crystalline lens to expand the depth of focus, correct myopia, and at the same time provide a certain degree of adjustment ability. The surface is smooth without sharp changes, does not cause glare and halos, corrects the patient's myopia and presbyopia at the same time, and has excellent visual effects.

[0022] 2. The present invention adopts a free-form surface instead of the spherical or aspherical surface of the ordinary intraocular lens with a crystalline lens, effectively limits the thickness of the lens, and is more versatile.

[0023] 3. The intraocular lens with a crystalline lens of the present invention is integrally formed, has a simple structure, is suitable for the complex intraocular liquid environment, has good stability, and is not likely to induce complications.

Brief Description of the Drawings

[0024] The drawings are only illustrative and cannot be regarded as a limitation to the present invention. For better explaining this embodiment, some components in the drawings are omitted, enlarged or reduced, and do not represent the dimensions of the actual product. Even if some known structures and their descriptions are omitted in the drawings, those skilled in the art can understand them.

Figure 1

Figure 2

Figure 3

Figure 4

Embodiments for Carrying Out the Invention

[0025] Hereinafter, in order to make the objectives, technical solutions and advantages of the embodiments of the present invention clearer, with reference to the drawings of the embodiments of the present invention, the technical solutions according to the embodiments of the present invention will be clearly and completely described. Needless to say, the described embodiments are some embodiments of the present invention, not all embodiments. All other embodiments obtained by those skilled in the art based on the embodiments of the present invention without creative work fall within the protection scope of the present invention.

[0026] (Embodiment 1) For the sake of understanding, referring to FIG. 1, an embodiment of an intraocular lens with extended depth of focus 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 of an integrated structure integrally formed of the same material. The optical part 1 is located between the first support part 2 and the second support part 3. The optical part 1 consists of two optical surfaces. One optical surface is a plane, and the other optical surface is a free-form surface having a function of extending the depth of focus.

[0027] By the geometric iteration method, the free-form surface is divided into a series of partial curved surfaces to discretize the free-form surface. The discretized free-form surface is represented by the envelope surface of a series of partial curved surfaces. Since the free-form surface is rotationally symmetric, here only the partial curved surface on one meridian is considered as the representative of all partial curved surfaces. After the incident light ray is refracted through the partial curved surface A0 in TIFF0007714809000004.tif31170, it is focused on the focal point F on the optical axis. The coordinates of the focal point F are (0, f0), where f0 is the focal length of the focal point F. According to the geometric relationship between the focal position of the partial curved surface A0 and the optical axis, the angle θ1 formed by the outgoing light ray of the partial curved surface A0 with respect to the optical axis is obtained. When θ1 is expressed by an equation, it is as follows. θ1 = arcsin(y0 / (f0 - z0)) (1) The incident light ray and the optical axis satisfy the following relational expression, TIFF0007714809000005.tif87170

[0028] In addition, solving the angle γ0 formed by the normal direction of the partial curved surface A with respect to the optical axis by simultaneously solving equations (2) and (3) is to be derived from the equivalent relational expressions of equations (2) and (3), and the derivation process is as follows. Refer to Figure 3. i ∵β1 = γ0 ∴n1sinβ1 = n1sinγ0 = n2sinβ2 ∵θ1 + γ0 = β2 ∴n1sinγ0 = n2sin(θ1 + γ0) ∴n1 / n2sinγ0 = sinθ1cosγ0 + sinγ0cosθ1 ∴(n1 / n2 - cosθ1)sinγ0 = sinθ1cosγ0 ∴sinγ0 / cosγ0 = tanγ0 = sinθ1 / (n1 / n2 - cosθ1) ∴γ0 = arctan(sinθ1 / (n1 / n2 - cosθ1))

[0029] Specifically, the optical part 1 is made of hydrophilic polyacrylate and has a refractive index of 1.437 at 35°C.

[0030] A method for manufacturing an intraocular lens for posterior chamber of the eye with extended depth of focus, including the following steps for designing the above intraocular lens for posterior chamber of the eye with extended depth of focus, S1: Optical design, determining the focal refractive power, effective optical part diameter, and extended depth of focus value of the optical part 1, modeling in zemax, using the free curved surface before discretization as the basic spherical surface, and optimizing to obtain the curvature r of the basic spherical surface that satisfies the focal refractive power requirement of the optical part 1, and calculating the focal distance range f of the optical part 1 from the focal refractive power of the optical part 1 最小 ~f 最大 and f 最小 = 1 / φ f 最大 = 1 / (φ + φ 拡張 )(5) In the formula, f 最小 , f 最大 are respectively the minimum focal length and the maximum focal length of the optical unit 1, φ, φ 拡張 are respectively the focal refractive power and the extended focal refractive power of the optical unit 1, Set the number of geometric iterations as i, discretize the basic spherical surface obtained by optimization. Since the intraocular lens is rotationally symmetric, the number of partial surfaces A0 on one meridian is i. Calculate the positions of the center points of all partial surfaces A0, and use A i to represent any partial surface on one meridian, and use (y i , z i ) to represent the position of the center point of any partial surface A0. Use f i to represent the focal length of any partial surface A i . Divide the focal length range f1~f i . Here, the absolute value gradually increases from f1 to f i . To prevent interference by incident light rays, take into account the constriction and dilation of the pupil, and reduce the dependence on the pupil. Therefore, from the center to the outside, the absolute value of the focal length f i of the partial surface A i gradually increases. Perform modeling by the geometric iteration method in matlab. From the focal length f i of the partial surface A i and the position of the center point of the partial surface A i (y i , z i ), obtain the angle θ i formed by the outgoing light ray of the partial surface A i with respect to the optical axis. TIFF0007714809000006.tif28170S2: It is turning processing. Based on the freeform surface designed in step S1, create a lathe program for the hydrophilic material, and use the single-point cutting technology with diamond to obtain the optical unit 1 by turning processing. Create a milling machine program, and obtain the shape of the optical region of the optical unit 1 and the legs of the first support part 2 and the second support part 3 by milling processing. S3: It is polishing treatment. Use a low-temperature cylinder to polish the intraocular lens. S4: Verification by testing, where the intraocular lens is analyzed and tested in an artificial eye system.

[0031] By introducing a freeform surface, the present invention uses a depth-of-focus extension technique for an intraocular lens in an aphakic eye to extend the depth of focus, correct myopia, and at the same time provide a certain degree of accommodation ability. The surface is smooth without abrupt changes, does not cause glare and halos, corrects the patient's myopia and presbyopia at the same time, and realizes clear vision for the patient.

[0032] Note that presbyopia occurs when the accommodation ability of the patient's eye lens weakens. The lens of the present invention provides a certain degree of accommodation ability to realize the correction of presbyopia. The accommodation ability is the extended depth of focus. Even when the patient's distance vision is completely corrected and they do not use the accommodation function of their own lens, they can still see clearly in a relatively large range of focal refractive power (+1D to +2.5D).

[0033] (Example 2) Specifically, based on Example 1, specific examples are used to explain the technical solution, and the effect of the technical solution is further expressed. Specifically, it is as follows. The manufacturing method of the aphakic posterior chamber intraocular lens of this example is as follows. (1) Overall design: It is determined that the focal refractive power of the intraocular lens is -10D, the optical part diameter is 5mm, and the extended depth of focus is -1D. (2) Optical design: Based on the preset focal refractive power of the intraocular lens and the area of the optical region (determined from the optical part diameter), it is modeled and optimized in zemax to obtain the curvature r = 10.4mm of the basic spherical surface, which is a concave surface. Calculated by Equation (5), the focal distance range is obtained as -100mm to -111.11mm. The number of geometric iterations is set to 100, and the basic spherical surface is discretized. Since the intraocular lens has rotational symmetry, the number of partial surfaces on one meridian is 100. Calculate the central positions of a series of partial surfaces, and from the inside to the outside, A1(y1,z1) to A 100 (y 100 ,z 100and divides the focal length range as follows, f1 = -100 mm f2 = -100.11 mm f3 = -100.22 mm … f 100 = -111.11 mm To prevent interference by incident light rays, consider the constriction and dilation of the pupil, and reduce the dependence on the pupil, the partial surface A gradually moves from the center to the outside i The focal length f i of which the absolute value gradually increases, Perform modeling by the geometric iteration method in Matlab, and from the focal length f i of the partial surface A i and the position of the center point of the partial surface A i (y i , z i ), find the angle θ i formed by the outgoing light ray of the partial surface A with respect to the optical axis i , TIFF0007714809000007.tif28170(3) is a turning process. Based on the freeform surface, create a lathe program for the hydrophilic material, use the single-point cutting technology with diamond, obtain the optical part by turning, create a milling machine program, and obtain the shape of the optical region of the optical part 1 and the legs of the first support part 2 and the second support part 3 by milling, (4) is a polishing process. Using the method of low-temperature cylindrical polishing, obtain an intraocular lens whose optical surface meets the standard, (5) is verification by testing. Analyze and test in a simulated eye system. Introduce the phakic posterior chamber intraocular lens of this embodiment into the eye model defined by ISO11979-2 and test it with an optical instrument to obtain the MTF value of defocus.

[0034] (Example 3) Specifically, based on Example 1, use specific examples to explain the technical solution and further demonstrate the effect of the technical solution. Specifically, it is as follows. The manufacturing method of the phakic posterior chamber intraocular lens of this embodiment is as follows. (1) Overall design, the refractive power of the intraocular lens is -15D, the diameter of the optical part is 5.5mm, and the extended depth of focus is determined to be -1.5D. (2) Optical design, modeled and optimized in zemax based on the preset refractive power and diameter of the optical part of the intraocular lens, to obtain the curvature r = 6.93mm of the basic spherical surface, which is a concave surface, calculated by formula (5), and the focal length range is obtained as -66.67mm to -60.6mm. Set the number of geometric iterations to 150, discretize the basic spherical surface. Since the lens has rotational symmetry, the number of partial surfaces on one meridian is 150. Calculate the central positions of a series of partial surfaces, from the inside to the outside, A1(y1,z1)~A 150 (y 150 ,z 150 ). Divide the focal length range as follows: f1 = -60.6mm f2 = -60.646mm f3 = -60.687mm … f 150 = -66.667mm To prevent interference by incident light and take into account the constriction and dilation of the pupil, and reduce the dependence on the pupil, from the center to the outside, the absolute value of the focal length f i of the partial surface A i gradually increases. Perform modeling by the geometric iteration method in matlab. From the focal length f i of the partial surface A i and the position of the center point of the partial surface A i (y i ,z i ), obtain the angle θ i formed by the outgoing ray of the partial surface A i with respect to the optical axis. (3) Turn-mill machining. Based on the free-form surface, create a lathe program for the hydrophilic material, use the single-point cutting technology with diamond, obtain the optical part by lathe machining, create a milling machine program, and obtain the shape of the optical region of the optical part 1 and the legs of the first support part 2 and the second support part 3 by milling. (4) A grinding process, using the method of low-temperature cylindrical grinding, to obtain an intraocular lens whose optical surface meets the standard, (5) Verification by testing, analyzing and testing in a simulated eye system. The phakic posterior chamber intraocular lens of this example is introduced into the eye model defined in ISO11979-2 and tested with an optical instrument to obtain the MTF value of defocus.

[0035] (Example 4) Specifically, based on Example 1, specific examples are used to explain the technical solutions, and the effects of the technical solutions are further expressed. Specifically, it is as follows. The manufacturing method of the phakic posterior chamber intraocular lens of this example is as follows. (1) Overall design, determining that the refractive power of the intraocular lens is -20D, the optical part diameter is 5mm, and the extended depth of focus is -1.75D, (2) Optical design, modeled and optimized in zemax according to the preset refractive power and optical part diameter of the intraocular lens to obtain the curvature r = 5.2mm of the basic spherical surface, which is a concave surface, calculated by formula (5), and the focal length range is obtained as -50mm to -45.98mm. Set the number of geometric iterations to 175, discretize the basic spherical surface. Since the lens has rotational symmetry, the number of partial surfaces on one meridian is 175, calculate the central positions of a series of partial surfaces, from the inside to the outside, A1(y1,z1)~A 175 (y 175 ,z 175 ), and divide the focal length range as follows, f1 = -45.977mm f2 = -46mm f3 = -46.023mm … f 175 = -50mm To prevent interference by incident light, consider the constriction and dilation of the pupil, and reduce the dependence on the pupil, from the center to the outside, the absolute value of the focal length f i of the partial surface A i gradually increases, Modeling is performed by geometric iteration method in Matlab for the partial surface A i The focal length f i and the position of the center point of the partial surface A i (y i , z i ), from which the angle θ i formed by the outgoing ray of the partial surface A with respect to the optical axis is obtained, i and TIFF0007714809000009.tif28170(3) Turning machining, creating a lathe program for a hydrophilic material based on a free-form surface, using a single-point cutting technique with diamond, obtaining an optical part by lathe machining, creating a milling machine program, and obtaining the shape of the optical region of the optical part 1 and the legs of the first support part 2 and the second support part 3 by milling, (4) Polishing treatment, using the method of low-temperature cylindrical polishing to obtain an intraocular lens whose optical surface meets the standard, (5) Verification by testing, analyzing and testing in a simulated eye system. The intraocular lens with a crystalline lens posterior chamber of this example is introduced into the eye model defined in ISO11979-2 and tested with an optical instrument to obtain the MTF value of defocus.

[0036] It should be noted that in the above examples, both the center point and the normal vector are represented by two points, which is the coordinate representation in the YZ coordinate system, and the X coordinate is omitted.

[0037] Needless to say, the above examples of the present invention are merely examples given to clearly explain the present invention and are not limitations on the embodiments of the present invention. Those skilled in the art can make various other forms of changes or corrections based on the above description. It is not necessary to list all embodiments here, nor is it possible to do so. When corrections, equivalent replacements, improvements, etc. are made without departing from the spirit and principles of the present invention, any of them shall be included in the protection scope of the claims of the present invention.

Claims

1. An intraocular lens for posterior chamber of the eye with extended depth of focus, comprising: an optical portion (1), a first support portion (2), and a second support portion (3), wherein the optical portion (1), the first support portion (2), and the second support portion (3) are integrally formed of the same material and have an integral structure, the optical portion (1) is located between the first support portion (2) and the second support portion (3), the optical portion (1) consists of two optical surfaces, one optical surface is a plane, and the other optical surface is a free-form surface having a depth of focus extension function; one optical surface of the optical portion (1) satisfies the design principle of the free-form surface, and the determination method thereof is to establish an arbitrary orthogonal coordinate system in space 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 free-form surface; The process of designing the free-form surface is as follows: By the geometric iteration method, the free-form surface is divided into a series of partial surfaces to discretize the free-form surface, and the discretized free-form surface is represented by the envelope surface of a series of partial surfaces. Since the free-form surface is rotationally symmetric, only the partial surface on one meridian is considered here as the representative of all partial surfaces; One partial surface A0 on the free-form surface is known, and its incident light vector and normal vector

2. The focal length f of the optical part (1) ０ is determined by the refractive power of the optical part (1), and the range of the refractive power is from 0 D to -30 D. The intraocular lens for expanding the depth of focus according to claim 1, characterized in that.

3. The intraocular lens for posterior chamber of the eye with extended depth of focus according to claim 1, wherein the range of the effective optical diameter of the optical portion (1) is 4 mm to 6 mm.

4. The intraocular lens for posterior chamber of the eye with extended depth of focus according to claim 1, wherein the extended depth of focus range of the optical portion (1) is -1 D to -2.5 D.

5. The intraocular lens for posterior chamber of the eye with extended depth of focus according to claim 1, wherein the optical portion (1) is made of hydrophilic polyacrylate.

6. The intraocular lens for posterior chamber of the eye with extended depth of focus according to claim 1, wherein the refractive index of the optical portion (1) at 35°C is 1.

437.

7. The intraocular lens for posterior chamber of the eye with extended depth of focus according to claim 1, wherein the thicknesses of the first support portion (2) and the second support portion (3) are both 0.08 mm to 0.15 mm.

8. A method for manufacturing an intraocular lens for posterior chamber of the eye with extended depth of focus according to any one of claims 1 to 7, comprising: the following steps: S1: Optical design, which determines the focal refractive power, effective optical part diameter, and extended focal depth value of the optical part (1), models it in zemax, uses the freeform surface before discretization as the basic spherical surface, optimizes it to obtain the curvature r of the basic spherical surface that meets the focal refractive power requirement of the optical part (1), and calculates the focal distance range f 最小 ~f 最大 of the optical part (1) from the focal refractive power of the optical part (1), and f 最小 = 1 / φ f 最大 = 1 / (φ + φ 拡張 )(5) where f 最小 , f 最大 are respectively the minimum focal length and the maximum focal length of the optical unit (1), and φ, φ 拡張 are respectively the focal refractive power and the extended focal refractive power of the optical unit (1), Set the number of geometric repetitions to i, discretize the optimized basic spherical surface, and since the intraocular lens is rotationally symmetric, the partial surface A on one meridian ０ The number of will be i, and for all partial surfaces A ０ Calculate the positions of the center points, and represent any partial surface on one meridian in A ｉ , (y ｉ , z ｉ ) represents the position of the center point of any partial surface A ０ , f ｉ represents the focal length of any partial surface A ｉ , and divide the focal length range f １ to f ｉ . Here, the absolute value gradually increases from f １ to f ｉ to prevent interference by the incident light, take into account the constriction and dilation of the pupil, and reduce the dependence on the pupil. Therefore, from the center to the outside, the absolute value of the focal length f ｉ of the partial surface A ｉ gradually increases, Perform modeling by geometric iteration method in Matlab for the partial surface A ｉ The focal length f ｉ and the position of the center point of the partial surface A ｉ (y ｉ , z ｉ ) to find the angle θ ｉ formed by the outgoing ray of the partial surface A with respect to the optical axis ｉ and obtain

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