An intraocular lens with a crystalline lens

Abstract

The application provides a phakic intraocular lens, and relates to the technical field of medical devices. The phakic intraocular lens comprises an optical main body having a front surface and a non-spherical rear surface; a support part arranged around the optical main body; and a transition part arranged between the optical main body and the support part; the front surface and the rear surface of the transition part are connected with the front surface and the rear surface of the optical main body respectively, and the radius of curvature of the front surface of the transition part is greater than the radius of curvature of the rear surface of the transition part. The application can reduce the appearance of an aperture, improve imaging quality and stability, and improve safety after implantation and reduce the risk of intraocular lens jamming.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and more specifically, to a phakic intraocular lens. Background Technology

[0002] Phakic intraocular lenses (PIOLs) can be categorized based on their optical design, including spherical, aspherical, toric, extended depth-of-focus, and multifocal types. Depending on their implantation location and fixation method, they can be classified as angle-supported PIOLs, iris-fixed PIOLs, and posterior chamber PIOLs. Posterior chamber PIOLs generally consist of an optical component and a support component, implanted between the iris and the natural lens. Due to their high surgical safety, rapid visual recovery, wide range of correction, fewer postoperative complications, and convenient aftercare, posterior chamber PIOLs hold a significant market position in refractive correction.

[0003] As the number of posterior chamber phakic intraocular lenses (IOLs) implanted continues to increase, some of their drawbacks have gradually become apparent. For example, the common spherical design of posterior chamber phakic IOLs not only introduces a large amount of spherical aberration, leading to glare in clinical practice; at the same time, because the space in the posterior chamber for placing the IOL is relatively narrow, the higher the optical power of a spherical phakic IOL, the closer its optical body edge will be to the natural lens, thus posing a risk of cataracts due to contact with the natural lens, and also limiting the corrective range of the product.

[0004] While existing phakic intraocular lenses (IOLs) utilize aspherical and biconcave designs to address some spherical aberration and contact issues between the optical body and the natural lens, they still present the following problems: Biconcave designs have limited applicability, only correcting high myopia; the edges of the optical body still pose a high risk of contact with the natural lens; furthermore, after posterior chamber IOLs are implanted, in low light or at night, when the pupil dilates beyond the IOL's optical body, light can directly pass through the transition between the optical body and the support structure, forming an aperture within the eye and affecting image quality; while increasing the size of the optical body can reduce the aperture, it often leads to a decrease in the dome height (i.e., the distance from the center point of the posterior surface of the PIOL's optical body to the human lens), increasing the safety and implantation risks associated with contact between the IOL and the natural lens, pupil, etc. In addition, after a posterior chamber phakic intraocular lens is implanted in the human eye, it is inevitable that the posterior chamber phakic intraocular lens will dislodge due to various accidents. In some cases, the supporting part of the lens is still behind the iris, while the main optical part in the middle is stuck in the pupil and protrudes from the iris, inevitably causing damage to the pupil and iris, requiring a second surgery to adjust the lens to the correct position. Summary of the Invention

[0005] The purpose of this invention is to solve the above-mentioned technical problems and provide a phakic intraocular lens that can reduce the appearance of halos, improve imaging quality and stability, and further enhance the safety after implantation in the human eye.

[0006] To achieve the above objectives, the present invention adopts the following technical solution:

[0007] A phakic intraocular lens, comprising:

[0008] An optical body comprising a front surface and a rear surface, wherein the rear surface has an aspherical shape;

[0009] The supporting portion, which is arranged around the optical body; and

[0010] A transition portion is disposed between the optical body and the support portion, wherein the radius of curvature of the front surface of the transition portion is greater than the radius of curvature of the rear surface of the transition portion, wherein the front surface of the transition portion is in contact with the front surface of the optical body, and the rear surface of the transition portion is in contact with the rear surface of the optical body.

[0011] To overcome the image quality degradation caused by aperture, this invention, through research, discovered that aperture is caused by the non-ideal refraction of incident light at the transition section between the optical body and the supporting part. The width of the transition section directly determines the aperture width in retinal imaging. This width is determined by the radius of curvature of the transition section near the front and rear surfaces of the optical body, as well as the surface shapes of the optical body and the supporting part. While maintaining a generally acceptable surface shape for the optical body and supporting part, the transition section near the front surface of the optical body comes into contact with the iris. If the radius of curvature is too small, the contact area with the iris will be too sharp, causing discomfort to the patient. Therefore, reducing the radius of curvature of the transition section near the rear surface of the optical body can eliminate the aperture effect and improve image quality.

[0012] Furthermore, the radius of curvature of the front surface of the transition portion ranges from 0.3 mm to 0.6 mm, and the radius of curvature of the rear surface of the transition portion ranges from 0.05 mm to 0.2 mm.

[0013] Furthermore, the transition portion has a protrusion on the side near the rear surface of the optical body that faces the front surface of the optical body.

[0014] Furthermore, the arch height of the optical body ranges from 0.4 mm to 0.6 mm, and after the phakic intraocular lens is implanted into the human eye, the distance between the transition portion and the natural lens ranges from 0.1 mm to 0.9 mm.

[0015] The present invention has discovered through research that the rear surface of the optical body has a protrusion facing the front surface of the optical body, which increases the distance between the protrusion of the transition portion and the natural lens, thus avoiding the risk of contact between the transition portion and the natural lens caused by the displacement of the optical body along the direction of the natural lens.

[0016] Furthermore, the rear surface profile of the optical body satisfies the following aspherical curve expression:

[0017] (I)

[0018] Where Z(y) is the expression for the curve of the posterior surface of the optical body and transition portion of the phakic intraocular lens on the YZ coordinate plane, c is the reciprocal of the radius of curvature of the spherical surface of the optical part, K ​​is the quadratic surface constant of the aspherical surface, Z is the vertical distance from any point on the curve to the horizontal axis Y, and A 2i For aspherical higher-order terms, K ranges from -220 to -0.2, and the higher-order term coefficient A4 ranges from -10e. -5 up to 1.2e -6 The coefficient of the higher-order term A6 is in the range of 4e. -4 up to 4.8e-4 The range of the coefficients A8 for higher-order terms is -9e. -5 to -7.5e -5 .

[0019] Furthermore, the front surface of the optical body of the phakic intraocular lens has one of the following shapes: torus, spherical, aspherical, or freeform.

[0020] Furthermore, the phakic intraocular lens has cut surfaces on both sides of the support portion away from the optical body along the direction of the main body diameter. The cut surfaces face the optical body, and the angle between the cut surfaces and the optical axis of the optical body is in the range of 30° to 50°. The cut surfaces are planar or curved.

[0021] This invention, through research, has discovered that setting cut surfaces on the sides of the support portion away from the optical main body not only avoids affecting the optical main body but also reduces the volume of the intraocular lens, facilitating implantation into the human eye and preventing damage to the iris during implantation surgery. Furthermore, when the posterior chamber phakic intraocular lens is blocked by the iris, the cut surfaces abut against the iris. Since the angle between the cut surfaces and the optical axis of the optical main body ranges from 30° to 50°, the contractile force of the iris on the posterior chamber phakic intraocular lens causes it to retract into the posterior chamber of the iris, avoiding the risk of being stuck.

[0022] Furthermore, the cut surface is formed from the edge of the support portion.

[0023] Furthermore, the thickness of the edge of the support portion ranges from 0.1 mm to 0.2 mm.

[0024] Furthermore, the support portion is provided with a haptic, and the phakic intraocular lens is implanted between the iris and the natural lens of the human eye, with the haptic embedded in the ciliary sulcus.

[0025] The beneficial effects of this invention are as follows:

[0026] (1) By reducing the radius of curvature of the rear surface of the transition part near the optical part to be smaller than the radius of curvature of the front surface of the transition part near the optical part, the present invention can achieve the effect of eliminating the aperture and improving the imaging quality while ensuring the arch height.

[0027] (2) The present invention further improves the distance between the transition portion and the natural lens (this distance is referred to herein as “edge arch height”) by providing protrusions on both sides of the rear surface of the optical body facing the front surface of the optical body. This can avoid the risk of contact between the optical body and the natural lens caused by the displacement of the optical body along the direction of the natural lens.

[0028] (3) Further research by the present invention has found that setting the cut surfaces on the sides of the support part away from the optical body can not only avoid the influence on the optical body, but also reduce the volume of the artificial lens, which is conducive to implantation into the human eye and avoids damage to the iris during implantation surgery; at the same time, when the phakic artificial lens is stuck by the iris, the phakic artificial lens can automatically retract to the posterior chamber of the iris, effectively reducing the risk of the phakic artificial lens being stuck and improving the stability and safety of implantation into the human eye. Attached Figure Description

[0029] Figure 1 This is a three-dimensional structural diagram of the phakic intraocular lens disclosed in this invention.

[0030] Figure 2 This is a side view of the phakic intraocular lens disclosed in this invention.

[0031] Figure 3 This is a schematic diagram of the formation of the aperture after implantation of an existing phakic intraocular lens.

[0032] Figure 4(a) is a schematic diagram of the transition portion of an existing phakic intraocular lens.

[0033] Figure 4(b) is a schematic diagram of the transition portion of an phakic intraocular lens according to an embodiment of the phakic intraocular lens disclosed in this invention.

[0034] Figure 5(a) is an imaging simulation diagram of an existing phakic intraocular lens.

[0035] Figure 5(b) is an imaging simulation diagram of an embodiment of the optimized transition portion of the phakic intraocular lens disclosed in this invention.

[0036] Figure 6 This is a schematic diagram of the edge arch and arch height of an embodiment of the phakic intraocular lens disclosed in this invention.

[0037] Figure 7 This is a schematic diagram of the edge arch height and arch height of existing intraocular lenses.

[0038] Figure 8 This is a comparison chart of the MTF performance of existing phakic intraocular lenses with a spherical design and the phakic intraocular lens disclosed in this invention, with a refractive power of 100 lp / mm at -3 D, -8 D, and -12 D.

[0039] Figure 9(a) is a schematic diagram of the support structure of an existing phakic intraocular lens.

[0040] Figure 9(b) is a schematic diagram of the support portion of the phakic intraocular lens disclosed in this invention.

[0041] Figure 10(a) is a cross-sectional schematic diagram of an existing phakic intraocular lens when it is stuck.

[0042] Figure 10(b) is a cross-sectional schematic diagram of the phakic intraocular lens stuck as disclosed in this invention.

[0043] Figure 11 This is a schematic diagram of the cross-sectional angle of the phakic intraocular lens disclosed in this invention.

[0044] The labels in the diagram have the following meanings: 1 is the main optical component; 2 is the supporting part; 3 is the transition part; 4 is the natural lens; 5 is the iris; 6 is the haptic; 7 is the cross-section; 8 is the edge of the supporting part; 9 is the protrusion. Detailed Implementation

[0045] To enable those skilled in the art to better understand the present invention, the technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort should fall within the scope of protection of the present invention.

[0046] Example 1

[0047] This embodiment provides a phakic intraocular lens disclosed in this invention, such as... Figure 1 and Figure 2 As shown, this phakic intraocular lens includes: an optical body 1, a support portion 2, and a transition portion 3. Specifically, the optical body 1 includes an anterior surface and a posterior surface (…). Figure 2 In the diagram, fs represents the front surface and rs represents the rear surface, where the rear surface rs has an aspherical shape; the support portion 2 is arranged around the optical body 1; the transition portion 3 is arranged between the optical body 1 and the support portion 2, and the radius of curvature of the front surface of the transition portion 3 is greater than the radius of curvature of the rear surface of the transition portion 3, wherein the front surface of the transition portion 3 is in contact with the front surface of the optical body 1, and the rear surface of the transition portion 3 is in contact with the rear surface of the optical body 1.

[0048] As an alternative, the radius of curvature of the front surface of the transition portion 3 ranges from 0.3 mm to 0.6 mm, and the radius of curvature of the rear surface of the transition portion 3 ranges from 0.05 mm to 0.2 mm.

[0049] As an optional solution, the posterior surface profile of the optical body 1 of the phakic intraocular lens satisfies the following aspherical curve expression:

[0050] (I)

[0051] Where Z(y) is the expression for the curve of the posterior surface of the optical body 1 and the transition part 3 of the intraocular lens on the YZ coordinate plane, c is the reciprocal of the radius of curvature of the spherical surface of the optical part, K ​​is the quadratic surface constant of the aspherical surface, Z is the vertical distance of any point on the curve from the horizontal axis Y, and A 2i The coefficients A4 are higher-order terms for aspherical surfaces. The values ​​of K and A are related to optical parameters such as the refractive index of the raw material, the Abbe number, and the optimization targets during optical design. For the PIOL disclosed in this invention, its optical power ranges from -21 D to -0.5 D, K ranges from -220 to -0.2, and the higher-order coefficients A4 range from -10e. -5 up to 1.2e -6 The coefficient of the higher-order term A6 is in the range of 4e. -4 up to 4.8e -4 The range of the coefficients A8 for higher-order terms is -9e. -5 to -7.5e -5 .

[0052] For example, aspherical phakic intraocular lenses with refractive powers of -3 D, -8 D, and -12 D, prepared using the aforementioned optical body 1 surface shape, are designated as test samples 1-3. Existing spherical phakic intraocular lenses (i.e., existing PIOLs) with the same refractive power are designated as test samples 4-6, and their MTF performance at 100 lp / mm is tested. In test samples 1-3, the arch height of the optical body 1 is 0.5 mm, and the distances from the transition portion 3 to the natural lens 4 are 0.51 mm, 0.51 mm, and 0.502 mm, respectively. In test samples 4-6, the distances from the transition portion 3 to the natural lens 4 are 0.49 mm, 0.48 mm, and 0.475 mm, respectively. The PIOL disclosed in this invention has a protrusion 9 facing the front surface of the optical body 1, while... Figure 7 The existing PIOL shown does not have a protrusion 9 facing the front surface of the optical body 1 on the side of its transition portion 3 near the rear surface of the optical body 1.

[0053] In this field, MTF, as a modulation transfer function, is used to describe the ability of an imaging system to transmit information at different spatial frequencies, that is, to measure the degree to which an optical system (such as a camera lens, telescope, etc.) reproduces the details of an object. The higher the MTF value, the stronger the ability of the imaging system to reproduce details; when the MTF value is 1, it means that the imaging system can perfectly reproduce the details of the object; when the MTF value is 0, it means that the imaging system cannot transmit information at that spatial frequency at all.

[0054] Figure 8The modulation transfer function results of test samples 1-3 and 4-6 are shown. It can be seen that the MTF results of the disclosed aspheric phakic intraocular lens are better than the MTF results of the existing PIOL, which means that the aspheric design improves the imaging quality.

[0055] Test Example 1

[0056] Figure 3 This is a schematic diagram illustrating the formation of the aperture after implantation of an existing intraocular lens. Figure 3 In the diagram, A represents local magnification; B represents the aperture; C represents the image; and D represents the retina. (Refer to the diagram.) Figure 3 It can be observed that aperture B is formed by the non-ideal refraction of incident light by the transition portion 3 between the optical body 1 and the supporting portion 2, resulting in an image on the fundus. The size of the aperture is directly related to the size of the transition portion 3.

[0057] In this test example, the PIOL used for comparison had an unoptimized radius of curvature of the transition portion 3 (as shown in Figure 4(a)). For example, the radius of curvature of the anterior surface of the transition portion 3 of the existing PIOL is 0.4 mm, and the radius of curvature of the posterior surface of the transition portion 3 is also 0.4 mm. Figure 4(b) shows a schematic diagram of the transition portion 3 of the phakic intraocular lens of the present invention. In Figures 4(a) and 4(b), A represents a partial magnification of the transition portion; R represents the radius of curvature of the anterior surface of the transition portion 3; and r represents the radius of curvature of the posterior surface of the transition portion 3. Figure 5(a) shows an imaging simulation obtained using imaging software for the existing PIOL used for comparison. It can be observed that the PIOL has a more obvious aperture Ic after imaging.

[0058] In this invention, the aperture Ic shown in Figure 5(a) is reduced by optimizing the radius of curvature of the posterior surface of the transition portion 3. Specifically, the radius of curvature of the posterior surface of the transition portion 3 can be optimized as a variable. For example, by reducing the radius of curvature of the posterior surface to be smaller than that of the anterior surface, in some embodiments, when the radius of curvature of the anterior surface is kept at 0.4 mm and the radius of curvature of the posterior surface is reduced to 0.06 mm, the aperture is no longer observed. Therefore, by optimizing the posterior surface radius of curvature to be smaller than that of the anterior surface, and thereby making the cross-sectional area of ​​the transition portion 3 of the intraocular lens reach the minimum value shown in Figure 4(b), the optimized intraocular lens can be simulated using imaging software. As shown in Figure 5(b), the aperture is reduced or even disappears during imaging of the optimized intraocular lens.

[0059] The phakic intraocular lens disclosed in this invention, depending on its optical power range (e.g., -21 D to -5 D), preferably has an anterior surface radius of curvature of 0.3 mm to 0.6 mm and a posterior surface radius of curvature of 0.05 mm to 0.2 mm. Matching the anterior surface radius of curvature of different transition portions 3 with the corresponding posterior surface radius of curvature minimizes the cross-sectional area of ​​the transition portion 3, thereby enabling phakic intraocular lenses of different optical powers to achieve the effect of minimizing or eliminating the aperture during imaging.

[0060] Example 2

[0061] In this embodiment, to further improve image quality after eliminating the aperture and reduce the risk of cataracts caused by contact between the artificial lens and the natural lens 4, as an optional solution, based on embodiment 1, such as... Figure 6 As shown, Figure 6 This is a schematic diagram of the phakic intraocular lens disclosed in this invention. Figure 6 In the figure, h represents the edge arch height, and H represents the arch height. The transition portion 3 has a protrusion 9 on the rear surface of the optical body 1, which faces the front surface of the optical body 1.

[0062] This invention, through research, has discovered that the rear surface of the optical body 1 can have a protrusion 9 facing the front surface of the optical body 1, thereby increasing the edge arch height h. This prevents the risk of contact between the transition portion 3 and the natural lens 4 caused by displacement of the optical body 1 along the direction of the natural lens 4, thus avoiding the probability of posterior cataracts. For example, when the optical power of the optical body 1 is -21 D to -0.5 D, the edge arch height h after the aspherical design disclosed in this invention is 0.001 mm to 0.02 mm higher than that of existing PIOLs.

[0063] As an optional solution, the optical body 1 has an optical power of -21 D to -0.5 D. The anterior surface of the optical body 1 of the phakic intraocular lens of the present invention has one of the following shapes: torus, spherical, aspherical, or freeform. The torus posterior chamber phakic intraocular lens is a special type of posterior chamber phakic intraocular lens. Its optical design mainly uses the anterior surface as a torus to achieve astigmatism correction, and the posterior surface as a spherical or aspherical surface to achieve myopia or hyperopia correction. Due to its diverse functions and wide range of applications, it is widely used.

[0064] Preferably, in the phakic intraocular lens of the present invention, the arch height of the optical body 1 is 0.4 mm to 0.6 mm, and the distance between the transition portion 3 and the natural lens 4 is 0.1 mm to 0.9 mm. The distance between the transition portion and the natural lens (marginal arch height) can be expressed by the following formula:

[0065] (II)

[0066] The final calculation results show that within the range of optical power -21 D to -0.5 D, the edge arch height will increase by 0.001 to 0.02 mm. Clinically, the arch height after implantation of posterior chamber refractive lenses is generally required to be greater than 0.25 mm. After optimization, the edge arch height can be increased by up to 8%, which provides better protection for the safety of patients after implantation. In this embodiment, the preferred arch height of the optical body 1 is 0.5 mm, and the distance between the transition part 3 and the natural lens 4 is 0.51 mm.

[0067] Example 3

[0068] Based on Embodiment 1 and / or Embodiment 2, in order to further improve the safety and stability of implantation and effectively reduce the risk of intraocular lens dislodgement, as an optional solution, a cross-section 7 is provided on both sides of the support portion 2 away from the optical body 1 along the direction of the main body diameter (as shown in Figure 9(b)). The cross-section 7 faces the optical body 1. The cross-section 7 is a plane or a curved surface, preferably a curved surface. The angle θ between the cross-section 7 and the optical axis of the optical body 1 is in the range of 30° to 50°.

[0069] As an optional solution, the support part 2 is provided with a haptic 6. In this invention, the phakic intraocular lens is implanted between the iris 5 and the natural lens 4 of the human eye, and the haptic 6 is embedded in the ciliary sulcus.

[0070] As an optional solution, Figure 11 This is a schematic cross-sectional view 7 of the phakic intraocular lens of the present invention. The thickness d of the edge 8 of the supporting portion is preferably in the range of 0.1 mm to 0.2 mm. Figure 11 In this context, θ represents the angle between the cut surface 7 and the optical axis of the optical body 1, preferably ranging from 30° to 50°. Figure 11 As shown, the cross-section 7 is formed from the edge of the support portion 2 along the direction toward the optical axis of the optical body 1 (e.g., θ=30°).

[0071] Through research, this invention has discovered that by providing cut surfaces 7 on both sides of the support portion 2 away from the optical body 1 along the direction of the main body diameter, it is possible not only to avoid affecting the optical body 1, but also to reduce the volume of the artificial lens, which is beneficial for implantation into the human eye and avoids damage to the iris 5 during implantation surgery. At the same time, when the phakic artificial lens of this invention is contacted and stuck by the iris 5, the cut surfaces 7 abut against the iris 5. Due to the angle between the cut surfaces 7 and the optical axis of the optical body 1, the contractile force of the iris 5 on the phakic artificial lens causes the phakic artificial lens of this invention to retract into the posterior chamber of the iris 5, avoiding the risk of being stuck.

[0072] The specific principle is as follows. Referring to Figures 9(a) and 9(b), where AA represents a cross-section, as shown in Figure 9(a), when the existing PIOL is rolled up in the injector, there are sharp edges on both sides, making rolling difficult. As shown in Figure 9(b), the phakic intraocular lens disclosed in this invention has a cut surface 7. Because the sharp edges on both sides are removed, the rolled-up intraocular lens occupies less space and its shape is closer to a cylinder. The intraocular lens will not deform or be damaged due to compression. Secondly, after the phakic intraocular lens is implanted into the anterior chamber of the eye, it needs to pass through the pupil during the process of adjusting it to the posterior chamber. By setting the cut surface 7 to optimize and thin the two sides of the PIOL, both the sharp edges are eliminated and the space occupied is reduced. Therefore, the compression and scraping of the pupil during the process of passing through the pupil becomes smaller and gentler, improving the safety and convenience of the surgeon's operation.

[0073] Furthermore, to prevent the PIOL from dislodging from the pupil after implantation due to various unforeseen circumstances, it can autonomously reposition itself along the oblique edge of the cut surface 7 under the pressure of pupillary contraction, preventing it from becoming stuck within the pupil. This largely avoids accidental pupillary damage. As shown in Figure 10(a), when the PIOL is stuck, viewed from the side, without the oblique edge formed by the cut surface 7, the PIOL will be compressed by the pupillary contraction force f and arch upwards along direction D1, undoubtedly posing a significant risk of damage to the iris 5. However, in the design with the cut surface 7, as shown in Figure 10(b), when the PIOL is stuck, under the action of the pupillary contraction force f, the PIOL will retract along direction D2 into the posterior chamber of the iris 5, avoiding the risk of the PIOL becoming stuck.

[0074] like Figure 11 As shown, considering the structural stability of the PIOL itself, the normal diameter of the human pupil, and the diffusion diameter in a dark environment, the angle between the cut surface 7 and the optical axis of the optical body 1 ranges from 30° to 50°. An excessively large angle will affect its optical performance, while an excessively small angle will significantly weaken the effect of the cut surface 7. Furthermore, to ensure structural stability, the thickness left at the side edge after forming the cut surface 7 must not be less than the thickness of the haptic 6. Preferably, the cut surface 7 is located at the edge 8 of the support portion 2, where the angle between the cut surface 7 and the optical axis of the optical body 1 is 40°, and the thickness d of the edge 8 of the support portion is 0.15 mm.

[0075] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and not to limit the solutions. Although the present invention has been described in detail with reference to preferred embodiments, those skilled in the art should understand that modifications or equivalent substitutions can be made to the technical solutions of the present invention based on the understanding of the present invention, without departing from the spirit and scope of the technical solutions of the present invention, and all such modifications or substitutions should be covered within the scope of the claims of the present invention.

Claims

1. A phakic intraocular lens, characterized in that, It includes: An optical body comprising a front surface and a rear surface, wherein the rear surface has an aspherical shape; The supporting portion, which is arranged around the optical body; and A transition portion is disposed between the optical body and the support portion, wherein the radius of curvature of the front surface of the transition portion is greater than the radius of curvature of the rear surface of the transition portion, wherein the front surface of the transition portion is in contact with the front surface of the optical body, and the rear surface of the transition portion is in contact with the rear surface of the optical body. The transition portion has a protrusion facing the front surface of the optical body on the side near the rear surface of the optical body; Along the direction of the main body diameter, there are cut surfaces on both sides of the support portion away from the optical body, the cut surfaces facing the optical body, and the cut surfaces having an angle with the optical axis of the optical body.

2. The phakic intraocular lens according to claim 1, characterized in that, The radius of curvature of the front surface of the transition portion ranges from 0.3 mm to 0.6 mm, and the radius of curvature of the rear surface of the transition portion ranges from 0.05 mm to 0.2 mm.

3. The phakic intraocular lens according to claim 1, characterized in that, The arch height of the optical body ranges from 0.4 mm to 0.6 mm, and after the phakic intraocular lens is implanted into the human eye, the distance between the transition portion and the natural lens ranges from 0.1 mm to 0.9 mm.

4. The phakic intraocular lens according to claim 1, characterized in that, The rear surface profile of the optical body satisfies the following aspherical curve expression: （Ⅰ） Where Z(y) is the expression for the curve of the posterior surface of the optical body and transition portion of the phakic intraocular lens on the YZ coordinate plane, c is the reciprocal of the radius of curvature of the spherical surface of the optical part, K ​​is the quadratic surface constant of the aspherical surface, Z is the vertical distance from any point on the curve to the horizontal axis Y, and A 2i For aspherical higher-order terms, K ranges from -220 to -0.2, and the higher-order term coefficient A4 ranges from -10e. -5 up to 1.2e -6 The range of the coefficient A6 of the higher-order term is 4e. -4 up to 4.8e -4 The range of the coefficients A8 for higher-order terms is -9e. -5 to -7.5e -5 .

5. The phakic intraocular lens according to claim 1, characterized in that, The front surface of the optical body of the phakic intraocular lens has one of the following shapes: toroidal, spherical, aspherical, or freeform.

6. The phakic intraocular lens according to any one of claims 1 to 5, characterized in that, The angle between the cut surface and the optical axis of the optical body is in the range of 30° to 50°, and the cut surface is a plane or a curved surface.

7. The phakic intraocular lens according to claim 1, characterized in that, The cut surface is formed from the edge of the support portion.

8. The phakic intraocular lens according to claim 6, characterized in that, The thickness of the edge of the support portion ranges from 0.1 mm to 0.2 mm.

9. The phakic intraocular lens according to claim 6, characterized in that, The supporting part is provided with a haptic, and the phakic intraocular lens is implanted between the iris and the natural lens of the human eye, with the haptic embedded in the ciliary sulcus.

Images