A phakic intraocular lens based on spatial filtering and a preparation method thereof

Abstract

The present invention provides a phakic intraocular lens based on spatial filtering and a preparation method thereof. The phakic intraocular lens includes an optical body, and the optical body includes an optical surface and an optical surface with a spatial filtering structure. The spatial filtering structure satisfies a filtering function that can change the spatial spectrum of the imaging light beam to expand the depth of focus. The present invention regards the imaging process that is usually refracted by geometric optical rays as an imaging process of wavefront transformation, and by introducing an optical surface with a spatial filtering structure in the phakic intraocular lens as a filter, changing the filtering function of the filtering structure can change the spatial spectrum structure of the imaging light beam, achieving the effects of expanding the depth of focus, enhancing dynamic vision, and simultaneously correcting myopia and presbyopia; having a better visual effect. Moreover, it has strong tolerance to adverse effects such as decentration and tilt; and has a simple structure and good stability.

Description

Technical Field

[0001] The present invention relates to the field of ophthalmic medical instruments and preparation technology, and in particular to a phakic intraocular lens based on spatial filtering and a preparation method thereof. Background Art

[0002] There are many factors that cause refractive errors in the human eye. The most common ones are bad eye habits, prolonged use of electronic devices, and fewer outdoor activities. People use their eyes at close range for a long time, which causes abnormal growth of the eye axis, thus causing refractive errors. Changes in the size of the eye axis caused by the aging of natural glasses can also cause refractive errors. With the development of ophthalmic technology and the improvement of human demand for vision, many corrective methods have emerged in modern society to restore patients' vision, such as laser surgery, traditional frame glasses, contact lenses, and lens implants. Compared with corneal laser surgery, traditional frame glasses, contact lenses and other correction methods, the implantable phakic intraocular lens (ICL) has the advantages of not damaging the cornea, not needing to be removed, and can be removed and replaced a second time, and is chosen by more and more young patients.

[0003] However, as myopic people age, the ciliary muscle's ability to adjust weakens, and presbyopia becomes a problem. A large number of patients will suffer from both myopia and presbyopia. Currently, there is no product on the domestic market that can correct both myopia and presbyopia at the same time. Related products on the international market use a concentric ring free-form surface refractive design, which has a poor effect on correcting presbyopia, and the image interference after correction is large, and the dynamic vision is poor, making it difficult to meet the patient's needs for exercise and driving. The Chinese invention patent with publication number CN115844587A discloses an extended depth of focus posterior chamber phakic intraocular lens and its preparation method, which introduces a free-form surface through a geometric iteration method, applies the depth of focus extension technology to the phakic intraocular lens, and extends the depth of focus. In order to enrich the development and application of posterior chamber phakic intraocular lenses, the shortcomings of the above-mentioned concentric ring free-form surface refractive design are overcome, and another posterior chamber phakic intraocular lens that can simultaneously solve myopia and presbyopia is developed, and the imaging quality of continuous vision is improved. Summary of the invention

[0004] The purpose of the present invention is to solve the above-mentioned technical problems and provide a phakic intraocular lens based on spatial filtering, which can simultaneously solve the problems of myopia and presbyopia and improve the imaging quality of continuous vision; another object of the present invention is to provide a method for preparing the phakic intraocular lens based on spatial filtering.

[0005] To achieve the above object, the present invention adopts the following technical solutions:

[0006] A phakic intraocular lens based on spatial filtering, comprising an optical body, the optical body including an optical surface and an optical surface having a spatial filtering structure, the spatial filtering structure satisfying a filtering function that can change the spatial spectrum of the imaging light beam to expand the depth of focus.

[0007] In the present invention, by introducing an optical surface with a spatial filtering structure into the phakic intraocular lens as a filter, changing the filtering function of the filtering structure can change the spatial spectrum structure of the imaging light beam, achieving the effect of expanding the depth of focus and simultaneously correcting myopia and presbyopia.

[0008] Further, the one optical surface is a spherical surface or an aspherical surface. Taking 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. The transverse coordinate axis X-axis and the coordinate axis Y-axis of the coordinate system are tangent to the optical surface. The surface shape of the aspherical surface satisfies the aspherical equation (Ⅰ) in the above Y-Z plane:

[0009]

[0010] where Z(y) is the curve expression of the aspherical surface in the two-dimensional coordinate system plane Y-Z, c is the reciprocal of the base spherical curvature radius of the aspherical surface, y is the perpendicular distance from any point on the curve to the transverse coordinate axis Z, A 2i is the aspherical high-order term coefficient, m and n are both integers not less than 1 and n>m, and K is the aspherical coefficient; when K and A 2i are 0, Z(y) is the spherical equation.

[0011] Further, in the X-Y plane, the filtering function H(x, y) satisfies equation (Ⅱ):

[0012]

[0013] where, represents the light wave function of the incident plane light; the represents the imaging light wave function;

[0014] The light wave function of the incident plane light is equation (Ш):

[0015]

[0016] where, is the modulus of the wave vector; A represents the amplitude, which is a constant and satisfies 0.5≤A≤3; is the initial phase of the incident plane light;

[0017] The imaging light wave function is equation (Ⅳ):

[0018]

[0019] where f is the focal length of the imaging lens.

[0020] Further, the filtering function H(x, y) is the transfer function of a Butterworth, Chebyshev, elliptic, or Bessel filter.

[0021] Further, the phakic intraocular lens based on spatial filtering further includes support loops located on the peripheral side of the optical body. The support loops include a first support loop and a second support loop, and the optical body and the support loops are integrally formed.

[0022] Further, the focal length f of the optical body is determined by the optical power of the optical body, and the optical power ranges from +3D to -21D.

[0023] Further, the effective optical zone area of the optical body ranges from 4.5 mm to 5.5 mm.

[0024] Further, the extended depth of focus of the optical body ranges from 1.0D to 2.5D.

[0025] Preferably, the optical body is made of hydrophilic polyacrylate.

[0026] Preferably, the refractive index of the optical body at 35 °C is 1.452.

[0027] Further, the thickness of the first support loop and the second support loop is from 0.08 mm to 0.15 mm.

[0028] The present invention also provides a method for preparing the above-mentioned phakic intraocular lens based on spatial filtering, including the following steps:

[0029] S1. Optical design: Determine the optical power and the effective optical zone area of the optical body; model in zemax and optimize the basic spherical surface; obtain the required imaging light wave function at this target extended depth of focus according to the light wave function of the incident light and the imaging light wave function passing through the basic spherical surface and the target extended depth of focus; obtain the filtering function H(x, y) according to the relationship between the filter and imaging; calculate the spatial filtering structure h of the filter according to the filtering function H(x, y);

[0030] The filtering function H(x, y) satisfies formula (II):

[0031]

[0032] , where, represents the light wave function of the incident plane light; the represents the imaging light wave function;

[0033] The light wave function of the incident plane light is formula (Ш):

[0034]

[0035] Among them, is the modulus of the wave vector; A represents the amplitude, which is a constant, usually 0.5 ≤ A ≤ 3; is the initial phase of the incident plane light;

[0036] The imaging light wave function is Equation (IV):

[0037]

[0038] where f is the focal length of the imaging lens;

[0039] S2. Turning and milling processing: According to the optical surface parameters of the optical design determined in step S1, write a lathe program for hydrophilic materials; use diamond single-point cutting technology to turn the optical main body; write a milling machine program to mill the outer shape of the optical zone and the loop feet;

[0040] S3. Perform low-temperature drum polishing treatment on the intraocular lens to obtain an implantable collamer lens based on spatial filtering.

[0041] The beneficial effects of the present invention are as follows:

[0042] (1) By introducing an optical surface with a spatial filtering structure into the implantable collamer lens, the present invention uses it as a filter. By changing the filtering function of the filtering structure, the spatial frequency spectrum structure of the imaging light beam can be changed, achieving the effects of extending the depth of focus and simultaneously correcting myopia and presbyopia.

[0043] (2) Based on the Abbe imaging theory, the present invention understands the imaging process that usually refracts from geometric optical rays as an imaging process of wavefront transformation. By introducing a spatial filtering structure and adjusting its filtering function, the depth of focus is extended, dynamic vision is enhanced, enabling the patient to correct presbyopia while correcting myopia and having a better visual effect.

[0044] (3) This implantable collamer lens is different from the concentric circle refraction design on the market, enhancing the tolerance of the lens to adverse effects such as eccentricity and tilt. Moreover, it has a simple structure, can be applicable to a complex eye fluid environment, has good stability, and is not easily induced to cause complications. Description of the Drawings

[0045] Figure 1 is a schematic structural diagram of the implantable collamer lens based on spatial filtering of the present invention.

[0046] Figure 1 Annotation: 1 is the optical main body; 2 is the supporting loop; 21 is the first supporting loop; 22 is the second supporting loop.

[0047] Figure 2The defocus MTF curve of the phakic intraocular lens in Comparative Example 1.

[0048] Figure 3 The defocus MTF curve of the phakic intraocular lens in Example 1.

[0049] Figure 4 It is the test chart of the phakic intraocular lens based on spatial filtering in Example 1 of the present invention on the USAF1951 resolution target;

[0050] Figure 4 In it, a, b, c, d, e, f, g, h respectively represent the imaging effects of the resolution target at intervals of 0.25 D between -12 D and -10.5 D.

[0051] Figure 5 The defocus MTF curve of the phakic intraocular lens in Comparative Example 2.

[0052] Figure 6 The defocus MTF curve of the phakic intraocular lens in Example 2.

[0053] Figure 7 It is the test chart of the phakic intraocular lens based on spatial filtering in Example 2 of the present invention on the USAF1951 resolution target;

[0054] Figure 7 In it, a, b, c, d, e, f respectively represent the imaging effects of the resolution target at intervals of 0.25 D between -8 D and -7 D. Detailed implementation manners

[0055] In order to enable those skilled in the art to better understand the solution of the present invention, the technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those of ordinary skill in the art without creative efforts shall fall within the protection scope of the present invention.

[0056] Example 1

[0057] As Figure 1As shown in the figure, this embodiment provides a phakic intraocular lens based on spatial filtering, which includes an optical body 1. The optical body 1 includes an optical surface and an optical surface with a spatial filtering structure. The spatial filtering structure satisfies a filtering function that can change the spatial spectrum of the imaging light beam to expand the depth of focus. As an optional solution, the phakic intraocular lens based on spatial filtering further includes a supporting loop 2 located on the peripheral side of the optical body 1. The supporting loop 2 includes a first supporting loop 21 and a second supporting loop 22, and the optical body 1 and the supporting loop 2 are integrally formed. Preferably, the thickness of the first supporting loop 21 and the second supporting loop 22 can be any thickness between 0.08 mm and 0.15 mm, such as 0.08 mm, 0.15 mm, 0.1 mm, etc.

[0058] One of the optical surfaces is spherical or aspherical. Taking 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. The horizontal coordinate axis X axis and the coordinate axis Y axis of the coordinate system are tangent to the optical surface. The surface shape of the aspherical surface satisfies the aspherical equation (Ⅰ) in the above Y-Z plane:

[0059]

[0060] where Z(y) is the curve expression of the aspherical surface in the two-dimensional coordinate plane Y-Z, c is the reciprocal of the base spherical curvature radius of the aspherical surface, y is the vertical distance from any point on the curve to the horizontal coordinate axis Z, A 2i is the aspherical high-order term coefficient, m and n are both integers not less than 1 and n>m, and K is the aspherical coefficient; when K and A 2i are 0, Z(y) is the spherical equation.

[0061] The spatial filtering structure satisfies a filtering function H(x, y) that can change the spatial spectrum of the imaging light beam to expand the depth of focus and satisfies equation (Ⅱ):

[0062]

[0063] where, represents the optical wave function of the incident plane light; the represents the imaging optical wave function;

[0064] The optical wave function of the incident plane light is equation (Ш):

[0065]

[0066] where, is the modulus of the wave vector; A represents the amplitude, which is a constant and satisfies 0.5≤A≤3; is the initial phase of the incident plane light;

[0067] The imaging light wave function is given by Equation (IV):

[0068]

[0069] where f is the focal length of the imaging lens.

[0070] As an alternative, the filtering function H(x, y) is the transfer function of a Butterworth, Chebyshev, elliptic, or Bessel filter, or a custom filtering function. After passing the incident light wave through the filter, the imaging effect is finally changed on the image plane to achieve the effect of extended depth of focus.

[0071] As an alternative, the focal length f of the optical body 1 is determined by the optical power of the optical body 1, and the optical power range is from +3D to -21D. The effective optical area range of the optical body 1 can be from 4.5 mm to 5.5 mm, and the extended depth of focus range of the optical body 1 is from 1.0D to 2.5D.

[0072] As an alternative, the optical body 1 is made of hydrophilic polyacrylate; the refractive index of the optical body 1 at 35 °C is 1.452. Of course, those skilled in the art can also adapt the material and refractive index according to actual needs.

[0073] The present invention also provides a method for preparing the phakic intraocular lens based on spatial filtering as described above, including the following steps:

[0074] S1. Optical design: Determine the optical power and effective optical area of the optical body 1; model in zemax and optimize the basic spherical surface; obtain the required imaging light wave function at this target extended depth of focus according to the light wave function of the incident light, its imaging light wave function passing through the basic spherical surface, and the target extended depth of focus; obtain the filtering function H(x, y) according to the relationship between the filter and imaging; calculate the spatial filtering structure h of the filter according to the filtering function H(x, y).

[0075] The filtering function H(x, y) satisfies Equation (II):

[0076]

[0077] , where represents the light wave function of the incident plane light; the represents the imaging light wave function;

[0078] The light wave function of the incident plane light is given by Equation (Ш):

[0079]

[0080] where is the modulus of the wave vector; A represents the amplitude, which is a constant, usually 0.5 ≤ A ≤ 3; is the initial phase of the incident plane light;

[0081] The imaging light wave function is given by Equation (IV):

[0082]

[0083] where f is the focal length of the imaging lens;

[0084] S2. Turning and milling: According to the optical surface parameters of the optical design determined in step S1, write a lathe program for the hydrophilic material; use diamond single-point cutting technology to turn the optical body 1; write a milling machine program to mill the outer shape of the optical zone and the loop feet.

[0085] S3. Perform low-temperature drum polishing on the intraocular lens to obtain a phakic intraocular lens based on spatial filtering.

[0086] Specifically, as Figure 1 shown, a phakic intraocular lens (ICL) based on spatial filtering includes an optical body 1, a first support loop 21, and a second support loop 22. The optical body 1 has an optical surface with a spatial filtering structure, and the spatial filtering structure satisfies a filtering function that can change the spatial spectrum of the imaging light beam to expand the depth of focus.

[0087] Among them, the optical body 1, the first support loop 21, and the second support loop 22 are of an integral structure, made of the same material, and integrally formed; the optical body 1 is made of hydrophilic polyacrylate with a refractive index of 1.443 at 35 °C.

[0088] The preparation method of the above-mentioned phakic intraocular lens based on spatial filtering is as follows:

[0089] S1. Optical design: Determine that the optical power of the optical body 1 is -12D and the effective optical zone area is 5.5 mm, and the target depth of focus extension is 1.5D; model in zemax and optimize the curvature r = 9.26 mm and aspheric coefficient K = -0.

[0090] 226, which is a concave surface, and the other surface is a plane; the incident light is plane light with an initial phase of 0 and an amplitude A = 1, and its light wave function is given by Equation (V):

[0091]

[0092] After passing through the basic lens, f = -0.0833, and the imaging light wave function is given by Equation (VI):

[0093]

[0094] According to the target depth of focus extension range of 1.5D, the required imaging light wave function can be obtained as Equation (VII):

[0095]

[0096] where b = 44 mm, which is the period; A1 is the amplitude. Since the amplitude is not modulated here, A1 = 1.

[0097] Since the relationship between the filter and imaging is as shown in Equation (II):

[0098]

[0099] Equation (VIII) can be obtained:

[0100]

[0101] According to the filtering function H(x, y), the spatial filtering structure h of the filter is calculated and superimposed on the base surface.

[0102] S2. Turning and milling: According to the optical surface parameters of the optical design, a lathe program for hydrophilic materials is written; using diamond single-point cutting technology, the optical main body 1 is turned; a milling machine program is written to mill the outer shape of the optical zone and the loop feet.

[0103] S3. Polishing treatment: Using the method of low-temperature drum polishing, an intraocular lens with a qualified optical surface is obtained.

[0104] Embodiment 2

[0105] As Figure 1 shown, a phakic intraocular lens (ICL) based on spatial filtering includes an optical main body 1, a first support loop 21 and a second support loop 22. The optical main body 1 has an optical surface with a spatial filtering structure, and the spatial filtering structure satisfies a filtering function that can change the spatial spectrum of the imaging light beam to expand the depth of focus.

[0106] Among them, the optical main body 1, the first support loop 21 and the second support loop 22 are of an integral structure, made of the same material and integrally formed; the optical main body 1 is made of hydrophilic polyacrylate with a refractive index of 1.443 at 35 °C.

[0107] The preparation method of the above phakic intraocular lens based on spatial filtering is as follows:

[0108] S1. Optical design:: Determine that the crystal power is -8 D, the optical zone area is 5 mm, and the depth of focus is expanded by 1 D; through the determined crystal power and optical zone area, a model is built in zemax, and the curvature r = 14.21 mm and the aspheric coefficient K = -1.315 of the base spherical surface are optimized. It is a concave surface, and the other surface is a plane; the incident light is a plane light with an initial phase of plane light with an amplitude A = 0.8, and its light wave function is Equation (IX):

[0109]

[0110] After passing through the basic lens, the imaging light wave function with f = -0.125 is Equation (VI):

[0111]

[0112] According to the extended depth of focus range of 1D, the required imaging light wave function can be obtained as Equation (VII):

[0113]

[0114] where b = 50 mm, which is the period; to enhance the extended depth of focus, the modulation amplitude A1 = 1.2.

[0115] Since the relationship between the filter and imaging satisfies Equation (II):

[0116]

[0117] Equation (VIII) can be obtained:

[0118]

[0119] According to the filtering function H(x, y), the spatial filtering structure h of the filter is calculated and superimposed on the basic surface.

[0120] S2. Turning and milling: According to the optical surface parameters of the optical design, a lathe program for hydrophilic materials is written; using diamond single-point cutting technology, the optical main body 1 is turned; a milling machine program is written to mill the outer shape of the optical zone and the loop feet.

[0121] S3. Polishing treatment: Using the method of low-temperature barrel polishing, an intraocular lens with a qualified optical surface is obtained.

[0122] Comparative Examples 1-2

[0123] A single-focus ICL with the same material and optical area as in Example 1 and the same optical power of -12D is fabricated as Comparative Example 1.

[0124] A single-focus ICL with the same material and optical area as in Example 1 and the same optical power of -8D as in Example 2 is fabricated as Comparative Example 2.

[0125] Test Example 1

[0126] (1) The Examples 1 and Comparative Example 1 are imported into the eye model required by ISO11979-2 and equipped with a 20D compensating lens, and the defocus MTF curves of the two are tested at 50 line pairs; the results of Comparative Example 1 are as Figure 2 shown, and the results of Example 1 are asFigure 3 As shown, it can be seen that compared with Comparative Example 1, the depth of focus range of Example 1 is larger, and the measured extended depth of focus is greater than 1.5D.

[0127] The ICL in Example 1 was introduced into the eye model required by ISO11979-2, equipped with a 20D compensating lens, and the USAF1951 resolution test chart was used to simulate imaging once at an interval of 0.25D, as Figure 4 shown. It can be seen that the ICL has a continuous depth of focus range between -12D and -10.5D.

[0128] (2) The ICLs of Example 2 and Comparative Example 2 were introduced into the eye model required by ISO11979-2, equipped with a 20D compensating lens, and the defocus MTF curves of the two were measured at 50 line pairs; the results of Comparative Example 2 are as Figure 5 shown, and the results of Example 1 are as Figure 6 shown. It can be seen that compared with Comparative Example 2, the depth of focus range of Example 2 is larger, and the measured extended depth of focus is greater than 1D.

[0129] The ICL in Example 2 was introduced into the eye model required by ISO11979-2, equipped with a 20D compensating lens, and the USAF1951 resolution test chart was used to simulate imaging once at an interval of 0.25D, as Figure 7 shown. It can be seen that the ICL has a continuous depth of focus range between -8D and -7D.

[0130] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention rather than to limit the solutions. Although the present invention has been described in detail with reference to the preferred embodiments, those of ordinary skill in the art should understand that, based on an understanding of the present solution, the technical solutions of the present invention can be modified or equivalently replaced without departing from the spirit and scope of the technical solutions of the present invention, and they should all be covered by the scope of the claims of the present invention.

Claims

1. A phakic intraocular lens based on spatial filtering, characterized in that, Comprising an optical body (1), the optical body (1) includes an optical surface and an optical surface with a spatial filtering structure, and the spatial filtering structure satisfies a filtering function that can change the spatial spectrum of the imaging light beam to expand the depth of focus; The filtering function satisfies Equation (II): （Ⅱ） Among them, represents the imaging light wave function; the represents the light wave function of the incident plane light; r represents the optical path. The light wave function of the incident plane light is Equation (Ш): (III) wherein, , is the modulus of the wave vector; A represents the amplitude, which is a constant and satisfies ; is the initial phase of the incident plane light; The light wave function of the imaging light is Equation (Ⅳ): （Ⅳ） Where f is the focal length of the imaging lens; where r0 represents the distance between the imaging point and the center of the lens, and K is the distance from the imaging point to the edge of the imaging range on the lens. Under paraxial conditions, r0 and K are approximately equal.

2. The phakic intraocular lens based on spatial filtering according to claim 1, wherein The one optical surface is a spherical surface or an aspherical surface. Taking 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. The horizontal coordinate axis X axis and the coordinate axis Y axis of the coordinate system are tangent to the optical surface. The surface shape of the aspherical surface satisfies the aspherical equation (Ⅰ) in the Y-Z plane: （Ⅰ） where \(Z(y)\) is the curve expression of the aspheric surface on the two-dimensional coordinate plane \(Y - Z\), \(c\) is the reciprocal of the base spherical curvature radius of the aspheric surface, \(y\) is the perpendicular distance from any point on the curve to the horizontal axis \(Z\), \(A\) 2i is the coefficient of the high-order term of the aspheric surface, \(m\) and \(n\) are both integers not less than 1 and \(n > m\), \(K\) is the aspheric coefficient; when \(K\) and \(A\) 2i are 0, \(Z(y)\) is the spherical equation.

3. The phakic intraocular lens based on spatial filtering according to claim 1, characterized in that, The filtering function is the transfer function of a Butterworth, Chebyshev, elliptic, or Bessel filter.

4. The phakic intraocular lens based on spatial filtering according to claim 1, wherein It further includes a support loop (2) located on the peripheral side of the optical body (1). The support loop (2) includes a first support loop (21) and a second support loop (22), and the optical body (1) and the support loop (2) are integrally formed.

5. The phakic intraocular lens based on spatial filtering according to claim 1, wherein The focal length f of the optical body (1) is determined by the optical power of the optical body (1), and the optical power range is from +3 D to -21 D.

6. The phakic intraocular lens based on spatial filtering according to claim 1, wherein The effective optical area range of the optical body (1) is from 4.5 mm to 5.5 mm.

7. The phakic intraocular lens based on spatial filtering according to claim 1, wherein The extended depth of focus range of the optical body (1) is from 1.0 D to 2.5 D.

8. The phakic intraocular lens based on spatial filtering according to claim 4, wherein, The thickness of the first support loop (21) and the second support loop (22) is from 0.08 mm to 0.15 mm.

9. The preparation method of the phakic intraocular lens based on spatial filtering according to any one of claims 1-8, comprising the following steps: S1. Optical design: Determine the optical power and the area of the effective optical zone of the optical body (1); model in zemax and optimize the basic spherical surface; obtain the required imaging light wave function under this target extended depth of focus according to the light wave function of the incident light, its imaging light wave function passing through the basic spherical surface, and the target extended depth of focus; obtain the filtering function according to the relationship between the filter and imaging ; According to the filtering function Calculate the spatial filtering structure of the filter ; The filtering function satisfies Equation (II): （Ⅱ）, Among them, represents the imaging light wave function; the represents the light wave function of the incident plane light; r represents the optical path; The light wave function of the incident plane light is Equation (Ш): (III) Among them, , is the modulus of the wave vector; A represents the amplitude, which is a constant, usually ; is the initial phase of the incident plane light; The light wave function of the imaging light is Equation (Ⅳ): （Ⅳ） Where f is the focal length of the imaging lens; where r0 represents the distance between the imaging point and the center of the lens, and K is the distance from the imaging point to the edge of the imaging range on the lens. Under paraxial conditions, r0 and K are approximately equal; S2. Turning and milling processing: According to the optical surface parameters of the optical design determined in step S1, write a lathe program for the hydrophilic material; use the diamond single-point cutting technology to turn the optical body (1); write a milling machine program to mill the outer shape of the optical zone and the loop feet; S3. Perform low-temperature barrel polishing treatment on the intraocular lens to obtain a phakic intraocular lens based on spatial filtering.

Images