Focal depth extended phakic posterior chamber intraocular lens and its manufacturing method

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 in particular to an extended depth of focus phakic posterior chamber intraocular lens and a method for manufacturing the same. [Background technology]

[0002] A phakic posterior chamber intraocular lens is an implantable intraocular lens (ICL) that is placed in the posterior chamber.

[0003] Poor eye habits, such as prolonged use of electronic devices, and reduced outdoor activities, cause the eyes to be used for long periods of time at close range, leading to abnormal elongation of the eye axis and resulting in refractive errors. With the development of technology and the increasing demand for vision, many corrective measures have been developed to restore patients' visual ability. Compared with corrective methods such as therapeutic laser keratectomy, traditional frame glasses, and contact lenses, phakic intraocular lenses have the advantages of not damaging the cornea, not needing to be put on and taken off, and being removable and replaceable, and are therefore being used by more and more young patients.

[0004] However, as myopic patients age, the ability of the ciliary muscle to adjust weakens, which causes the problem of presbyopia, and the patient suffers from not only myopia but also presbyopia. Conventional products or methods for correcting refractive errors such as myopia, presbyopia, and astigmatism, such as frame glasses, contact lenses, therapeutic laser keratectomy, and ICL implantation, cannot simultaneously correct myopia and presbyopia.

[0005] Therefore, it is a technical problem for those skilled in the art to design a phakic intraocular lens that can simultaneously solve the problems of myopia and presbyopia, thereby improving the visual quality of patients. Summary of the Invention [Problem to be solved by the invention]

[0006] The present invention provides an extended depth of focus type phakic posterior chamber intraocular lens that has the ability to extend and adjust the depth of focus and simultaneously solves the problems of myopia and presbyopia, and a manufacturing method thereof. [Means for solving the problem]

[0007] The technical solutions of the present invention to achieve the above effects are as follows: A depth of focus extended phakic posterior chamber intraocular lens including an optical portion, a first haptic portion, and a second haptic portion, the optical portion, the first haptic portion, and the second haptic portion being an integral structure integrally molded from the same material, the optical portion being located between the first haptic portion and the second haptic portion, the optical portion being composed of two optical surfaces, one optical surface being a flat surface and the other optical surface being a free-form surface having a depth of focus extended function.

[0008] Furthermore, one optical surface of the optical part satisfies the design principle of a free-form surface, and the method of determining this is as follows: A Cartesian coordinate system in an arbitrary space 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 free-form surface.

[0009] Furthermore, the process of designing the free-form surface is as follows. By using a geometric iteration method, the free-form surface is divided into a series of subsurfaces, and the free-form surface is discretized. The discretized free-form surface is expressed by the envelope of the series of subsurfaces. Since the free-form surface is rotationally symmetric, only the subsurface on one meridian is considered here as a representative of all the subsurfaces. A partial surface A0 on a free-form surface is known, and its incident ray vector and normal vector TIFF2025500986000002.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] TIFF2025500986000003.tif16170

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

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

[0014] Furthermore, the optic is made from a hydrophilic polyacrylate.

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

[0016] Furthermore, the first support portion and the second support portion each have a thickness of 0.08 mm to 0.15 mm.

[0017] A method for manufacturing an extended depth of focus type phakic posterior chamber intraocular lens, comprising the steps of: S1: Optical design, determining the focal power of the optical part, the effective optical part diameter and the extended focal depth value, modeling them in Zemax, optimizing the free curved surface before discretization as a base sphere to obtain the curvature r of the base sphere that satisfies the focal power requirements of the optical part, and calculating the focal length range f of the optical part from the focal power of the optical part. 最小 ~f 最大 Calculate f 最小 =1 / φ f 最大 =1 / (φ+φ 拡張 )(5) In the formula, f 最小 , f 最大 are the minimum and maximum focal lengths of the optical section (1), respectively, and φ and φ 拡張 are the focal power and the extended focal power of the optical part (1), respectively; The number of geometric iterations is set as i, and the optimized basic sphere is discretized. Since the intraocular lens is rotationally symmetric, the number of partial surfaces A0 on one meridian is obtained, which is i. The positions of the centers of all partial surfaces A0 are calculated, and A i Let us denote any subsurface on one meridian, and (y i ,z i) represents the position of the center point of any of the partial surfaces A0, and f i In any of the subsurfaces A i The focal length ranges from f1 to f i Divide f1 to f2, where i The absolute value gradually increases to prevent interference from incident light, and in order to reduce dependence on the pupil, the partial curve A is applied from the center to the outside, taking into consideration the contraction and expansion of the pupil. i The focal length f i The absolute value of gradually increases, A model was created using the geometric iteration method in Matlab, and the subsurface A i The focal length f i and the position A of the center point of the partial surface i (y i ,z i ) from the optical axis, i The angle θ of the emitted light beam i Seeking TIFF2025500986000004.tif28170S2: Turn-mill processing, in which a lathe program for a hydrophilic material is created based on the free-form surface designed in step S1, and an optical part is obtained by lathe processing using a single-point cutting technique with diamond, and a milling program is created, and the shape of the optical area of ​​the optical part and the legs of the first support and the second support are obtained by milling; S3: A polishing process in which the intraocular lens is polished using a low-temperature cylinder; S4: Verification by testing, in which the intraocular lens is analyzed and tested in a simulated eye system.

[0018] In addition, the normal vector of the partial surface passes through the partial surface and is perpendicular to the tangent plane of the partial surface, and the partial surface is a minute sphere, and the partial surface can be obtained by the geometric relationship of the normal vector of the partial surface. In step 1, the curvature r of the base sphere that meets the focal power requirements of the optical part is obtained by optimization, and the optimization is performed by adjusting the parameters of the base sphere 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 The corresponding focal length is fi It is. Effect of the Invention

[0020] Compared with the prior art, the beneficial effects of the technical solutions of the present invention are as follows: The present invention uses depth of focus extension technology in phakic intraocular lenses to go beyond correcting myopia and add depth of focus accommodative capabilities to the lens.

[0021] 1. The present invention applies depth of focus extension technology to phakic intraocular lenses by introducing freeform surfaces to extend the depth of focus, correct myopia while providing a certain degree of accommodation, the surface is smooth and has no abrupt changes, and does not cause glare and halos, so as to correct the patient's myopia while simultaneously correcting presbyopia, and the visual effect is excellent.

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

[0023] 3. The phakic intraocular lens of the present invention is integrally molded, has a simple structure, is compatible with the complex intraocular fluid environment, has good stability, and is less likely to induce complications. [Brief description of the drawings]

[0024] 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 schematic diagram of the front structure of a phakic intraocular lens provided by an embodiment of the present invention. [Diagram 2] FIG. 2 is a schematic diagram of the side structure of a phakic intraocular lens provided by an embodiment of the present invention. [Diagram 3]FIG. 3 is a light path diagram of a partial curved surface provided by an embodiment of the present invention. [Figure 4] FIG. 4 is a principle diagram of the focal depth extension provided by an embodiment of the present invention. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0025] 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.

[0026] Example 1 For ease of understanding, refer to FIG. 1, and one embodiment of a focal depth extended phakic posterior chamber intraocular lens provided by the present invention includes an optical portion 1, a first haptic portion 2, and a second haptic portion 3, and the optical portion 1, the first haptic portion 2, and the second haptic portion 3 are an integral structure integrally molded from the same material, the optical portion 1 is located between the first haptic portion 2 and the second haptic portion 3, and 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 focal depth extended function.

[0027] By using a geometric iteration method, the free-form surface is divided into a series of subsurfaces, and the free-form surface is discretized. The discretized free-form surface is expressed by the envelope of the series of subsurfaces. Since the free-form surface is rotationally symmetric, only the subsurface on one meridian is considered here as a representative of all the subsurfaces. TIFF2025500986000005.tif31170After the incident light ray is refracted through the partial curved surface A0, it is focused on a focal point F on the optical axis. The coordinates of the focal point F are (0, f0), and 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 of the outgoing light ray of the partial curved surface A0 with respect to the optical axis is obtained. The formula for θ1 is as follows: θ1=arcsin(y0 / (f0-z0))(1) The incident ray and the optical axis satisfy the following relationship: TIFF2025500986000006.tif87170

[0028] In addition, by simultaneously using equations (2) and (3), the partial curved surface A i The angle γ0 between the normal direction and the axis of the axis of the rotation axis is derived from the equivalent relation between equations (2) and (3). The process of derivation is as follows. See FIG. 3. ∵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 portion 1 is made of hydrophilic polyacrylate and has a refractive index of 1.437 at 35°C.

[0030] A method for manufacturing an extended depth of focus type phakic posterior chamber intraocular lens, comprising the steps of: S1: Optical design, determining the focal power, effective optical diameter and extended focal depth value of the optical part 1, modeling them in Zemax, optimizing the free curved surface before discretization as a base sphere to obtain a curvature r of the base sphere that satisfies the focal power requirements of the optical part 1, and calculating the focal length range f of the optical part 1 from the focal power of the optical part 1. 最小 ~f 最大 Calculate f 最小 =1 / φ f 最大 =1 / (φ+φ 拡張 )(5) In the formula, f 最小 , f 最大 are the minimum and maximum focal lengths of the optical unit 1, respectively, and φ, φ 拡張 are the focal power and the extended focal power of the optical part 1, respectively, The number of geometric iterations is set as i, and the optimized basic sphere is discretized. Since the intraocular lens is rotationally symmetric, the number of partial surfaces A0 on one meridian is obtained, which is i. The positions of the centers of all partial surfaces A0 are calculated, and A i Let us denote any subsurface on one meridian, and (y i ,z i ) represents the position of the center point of any of the partial surfaces A0, and f i In any of the subsurfaces A i The focal length ranges from f1 to f i Divide f1 to f2, where i The absolute value gradually increases to prevent interference from incident light, and in order to reduce dependence on the pupil, the partial curve A is applied from the center to the outside, taking into consideration the contraction and expansion of the pupil. i The focal length f i The absolute value of gradually increases, A model was created using the geometric iteration method in Matlab, and the subsurface A i The focal length f i and the position A of the center point of the partial surface i (y i ,z i ) from the optical axis, i The angle θ of the emitted light beam i Seeking TIFF2025500986000007.tif28170S2: Turn-mill processing, in which a lathe program for a hydrophilic material is created based on the free-form surface designed in step S1, and an optical portion 1 is obtained by lathe processing using a single-point cutting technique with diamond, and a milling program is created, and the shape of the optical area of ​​the optical portion 1 and the legs of the first support portion 2 and the second support portion 3 are obtained by milling processing, S3: A polishing process in which the intraocular lens is polished using a low-temperature cylinder; S4: Verification by testing, in which the intraocular lens is analyzed and tested in a simulated eye system.

[0031] The present invention applies depth of focus extension technology to phakic intraocular lenses by introducing freeform surfaces to extend the depth of focus, correct myopia while providing a certain degree of accommodation, the surface is smooth and free of abrupt changes, and does not cause glare and halos, correcting the patient's myopia while correcting presbyopia, thereby providing the patient with clear vision.

[0032] Presbyopia is caused by a weakening of the accommodative ability of the patient's eye's crystalline lens, and the lens of the present invention provides a certain degree of accommodative ability to correct presbyopia. Accommodative ability is an extended depth of focus, and the patient can still see clearly in a relatively large focal power range (+1D to +2.5D) without using the accommodative ability of his or her crystalline lens when his or her distance vision is fully corrected.

[0033] 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. The manufacturing method of the phakic posterior chamber intraocular lens of this embodiment is as follows. (1) determining the overall design of the intraocular lens, the focal power of which is -10D, the optic diameter of which is 5mm, and the extended depth of focus of which is -1D; (2) Optical design. According to the preset focal power and area of ​​the optical zone of the intraocular lens (determined from the optical zone diameter), the lens is modeled and optimized in Zemax to obtain the curvature r of the base sphere of 10.4 mm, which is concave and calculated by Equation (5). The focal length range is obtained to be -100 mm to -111.11 mm. The number of geometric iterations is set to 100 to discretize the base sphere. Since the intraocular lens is rotationally symmetric, the number of partial surfaces on one meridian is 100. The center positions of a series of partial surfaces are calculated, and the center positions are respectively A1(y1,z1) to A2 from the inside to the outside. 100 (y 100 ,z 100) and the focal length range is divided as follows: f1=-100mm f2=-100.11mm f3=-100.22mm … f 100 =-111.11mm In order to prevent interference from incident light, and to take into consideration the contraction and expansion of the pupil, partial curved surface A is used from the center to the outside to reduce dependency on the pupil. i Focal length f i The absolute value of gradually increases, A model was created using the geometric iteration method in Matlab, and the subsurface A i The focal length f i and the position A of the center point of the partial surface i (y i ,z i ) from the optical axis, i The angle θ of the emitted light beam i Seeking TIFF2025500986000008.tif28170(3) Turn-mill processing, creating a lathe program for a hydrophilic material based on a free curved surface, using a diamond one-point cutting technique to obtain an optical part by lathe processing, creating a milling program, and obtaining the shape of the optical area of ​​the optical part 1 and the legs of the first support part 2 and the second support part 3 by milling processing; (4) A polishing process, using a low-temperature cylindrical polishing method to obtain an intraocular lens whose optical surface meets the standard; (5) Verification by testing, which involves analysis and testing in a simulated eye system. The phakic posterior chamber intraocular lens of this embodiment is introduced into an eye model defined in ISO11979-2 and tested with an optical instrument to obtain the MTF value of defocus.

[0034] 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. The manufacturing method of the phakic posterior chamber intraocular lens of this embodiment is as follows. (1) determining the overall design of the intraocular lens to have a focal power of -15D, an optic diameter of 5.5mm, and an extended depth of focus of -1.5D; (2) Optical design. According to the preset focal power and optical diameter of the intraocular lens, the lens is modeled and optimized in Zemax to obtain the curvature r of the base sphere of 6.93 mm, which is concave. The focal length range is obtained to be -66.67 mm to -60.6 mm by calculating using formula (5). The number of geometric iterations is set to 150 to discretize the base sphere. Since the lens is rotationally symmetric, the number of partial surfaces on one meridian is 150. The center positions of a series of partial surfaces are calculated, and the center positions are respectively A1(y1,z1) to A2 from the inside to the outside. 150 (y 150 ,z 150 ) and the focal length range is divided as follows: f1=-60.6mm f2=-60.646mm f3=-60.687mm … f 150 =-66.667mm In order to prevent interference from incident light, and to take into consideration the contraction and expansion of the pupil, partial curved surface A is used from the center to the outside to reduce dependency on the pupil. i The focal length f i The absolute value of gradually increases, A model was created using the geometric iteration method in Matlab, and the subsurface A i The focal length f i and the position A of the center point of the partial surface i (y i ,z i ) from the optical axis, i The angle θ of the emitted light beam i Seeking TIFF2025500986000009.tif28170(3) Turn-mill processing, creating a lathe program for a hydrophilic material based on a free curved surface, using a diamond one-point cutting technique to obtain an optical part by lathe processing, creating a milling program, and obtaining the shape of the optical area of ​​the optical part 1 and the legs of the first support part 2 and the second support part 3 by milling processing; (4) A polishing process, using a low-temperature cylindrical polishing method to obtain an intraocular lens whose optical surface meets the standard; (5) Verification by testing, which involves analysis and testing in a simulated eye system. The phakic posterior chamber intraocular lens of this embodiment is introduced into an 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, a specific example is used to explain the technical solution, so as to better express the effect of the technical solution. The manufacturing method of the phakic posterior chamber intraocular lens of this embodiment is as follows. (1) determining the overall design of the intraocular lens, the focal power of which is −20D, the optic diameter of which is 5mm, and the extended depth of focus of which is −1.75D; (2) Optical design. According to the preset focal power and optical diameter of the intraocular lens, the lens is modeled and optimized in Zemax to obtain the curvature r of the base sphere of 5.2 mm, which is concave. The focal length range is calculated as -50 mm to -45.98 mm by using the formula (5). The number of geometric iterations is set to 175 to discretize the base sphere. Since the lens is rotationally symmetric, the number of partial surfaces on one meridian is 175. The center positions of the series of partial surfaces are calculated, and the center positions are respectively A1(y1,z1) to A2 from the inside to the outside. 175 (y 175 ,z 175 ) and the focal length range is divided as follows: f1=-45.977mm f2=-46mm f3=-46.023mm … f 175 =-50mm In order to prevent interference from incident light, and to take into consideration the contraction and expansion of the pupil, partial curved surface A is used from the center to the outside to reduce dependency on the pupil. i The focal length f i The absolute value of gradually increases, A model was created using the geometric iteration method in Matlab, and the subsurface A i The focal length f i and the position A of the center point of the partial surface i (y i ,z i ) from the optical axis, i The angle θ of the emitted light beam i Seeking TIFF2025500986000010.tif28170(3) Turn-mill processing, creating a lathe program for a hydrophilic material based on a free curved surface, using a diamond one-point cutting technique to obtain an optical part by lathe processing, creating a milling program, and obtaining the shape of the optical area of ​​the optical part 1 and the legs of the first support part 2 and the second support part 3 by milling processing; (4) A polishing process, using a low-temperature cylindrical polishing method to obtain an intraocular lens whose optical surface meets the standard; (5) Verification by testing, which involves analysis and testing in a simulated eye system. The phakic posterior chamber intraocular lens of this embodiment is introduced into an eye model defined in ISO11979-2 and tested with an optical instrument to obtain the MTF value of defocus.

[0036] In the above embodiment, the center point and the normal vector are both expressed as two points, and are expressed as coordinates in the YZ coordinate system, with the X coordinate being 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 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. 1. An extended depth of focus phakic posterior chamber intraocular lens, comprising:

1. A focal depth extended type phakic posterior chamber intraocular lens comprising an optical portion (1), a first support portion (2), and a second support portion (3), the optical portion (1), the first support portion (2), and the second support portion (3) being an integral structure integrally molded from the same material, the optical portion (1) being located between the first support portion (2) and the second support portion (3), the optical portion (1) being composed of two optical surfaces, one optical surface being a plane surface, and the other optical surface being a free-form surface having a focal depth extended function.

2. The focal depth extended type phakic posterior chamber intraocular lens according to claim 1, characterized in that one optical surface of the optical portion (1) satisfies the design principle of a free-form surface, and the method of determining this is to establish an orthogonal coordinate system in an arbitrary 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.

3. The process of designing the free-form surface is as follows: A geometric iteration method is used to discretize the free-form surface by dividing the free-form surface into a series of subsurfaces, and the discretized free-form surface is expressed as an envelope of the series of subsurfaces. Since the free-form surface is rotationally symmetric, only a subsurface on one meridian is considered here as a representative of all the subsurfaces; Incident light falls on partial curved surface A ０ After being refracted through the optical axis, the light is focused to a focal point F on the optical axis, and the coordinates of the focal point F are (0, f ０ ) and f ０ is the focal length of the focus F, and the partial surface A ０ Due to the geometric relationship between the focal position and the optical axis, ０ The angle θ of the emitted light beam １ Obtain θ １ The formula is as follows: θ １ [#]() ０ f ０  ０ )()) The incident light and the optical axis satisfy the following relationship: According to Snell's law, n １ sinβ １ =n ２ sinβ ２ (3) In the formula, n １ , n ２ are the refractive indices of the incident medium and the exit medium, respectively. The refractive indices of the incident medium and the exit medium are known quantities. The incident medium is an intraocular lens. The partial curved surface A ０ The angle γ ０ γ ０ can be expressed as follows: c ０ =arctan(sinth １ / (n １ / n ２ -cost １ ))(4)

4. The focal length f of the optical unit (1) ０ is determined by the focal power of the optical part (1), and the focal power ranges from 0D to -30D.

5. 2. The focal depth extended type phakic posterior chamber intraocular lens according to claim 1, wherein the effective optical zone diameter of the optical zone (1) is in the range of 4 mm to 6 mm.

6. The extended focal depth type phakic posterior chamber intraocular lens according to claim 1, characterized in that the extended focal depth range of the optical part (1) is -1D to -2.5D.

7. The extended depth of focus phakic posterior chamber intraocular lens according to claim 1, characterized in that the optical part (1) is made of hydrophilic polyacrylate.

8. 2. The focal depth extended type phakic posterior chamber intraocular lens according to claim 1, characterized in that the refractive index of the optical part (1) at 35° C. is 1.

437.

9. The focal depth extended type phakic posterior chamber intraocular lens according to claim 1, characterized in that the thickness of each of the first support portion (2) and the second support portion (3) is 0.08 mm to 0.15 mm.

10. A method for producing the focal depth extended type phakic posterior chamber intraocular lens according to any one of claims 1 to 9, comprising the steps of: The method includes the steps of: S1: Optical design, determining the focal power, effective optical diameter and extended focal depth value of the optical unit (1), modeling them in Zemax, and optimizing the free-form surface before discretization as a base sphere to obtain a curvature r of the base sphere that satisfies the focal power requirements of the optical unit (1), and calculating the focal length range f of the optical unit (1) from the focal power of the optical unit (1). 最小 ~f 最大 Calculate f 最小 =1 / φ f 最大 =1 / (φ+φ) 拡張 )(5) In the formula, f 最小 , f 最大 are the minimum and maximum focal lengths of the optical unit (1), respectively, and φ, φ 拡張 are the focal power and the extended focal power of the optical part (1), respectively; The number of geometric iterations is set as i, and the base sphere obtained by optimization is discretized. Since the intraocular lens is rotationally symmetric, a partial curved surface A on one meridian is ０ If we obtain the number of i, then all the partial surfaces A ０ Calculate the position of the center point of A ｉ Let us denote any partial surface on one meridian, and (y ｉ , z ｉ ) on any partial surface A ０ represents the position of the center point of ｉ In any partial surface A ｉ represents the focal length of the focal length range f １ ~f ｉ Divide f １ From f ｉ The absolute value gradually increases to prevent interference from incident light, take into consideration the contraction and expansion of the pupil, and reduce dependency on the pupil. ｉ The focal length f ｉ The absolute value of gradually increases, Modeling was performed using the geometric iteration method in Matlab, and partial surface A ｉ The focal length f ｉ and the position A of the center point of the partial surface ｉ (y ｉ , z ｉ ) from the partial curved surface A with respect to the optical axis ｉ The angle θ of the emitted light beam ｉ Seeking S2: Turn-mill processing. Based on the free-form surface designed in step S1, a lathe program for a hydrophilic material is created, and an optical portion (1) is obtained by lathe processing using a single-point cutting technique with diamond. A milling program is created, and the shape of the optical area of ​​the optical portion (1) and the legs of the first support portion (2) and the second support portion (3) are obtained by milling. S3: A polishing process, in which the intraocular lens is polished using a low-temperature cylinder; S4: Verification by testing, the method for manufacturing an extended depth of focus phakic posterior chamber intraocular lens, characterized in that the intraocular lens is analyzed and tested in a simulated eye system.

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