阅读说明：本技术 用于设计因amd丧失视力而为患者提供视力矫正的眼内透镜的方法及眼内透镜的定位机构 (Method for designing an intraocular lens for providing vision correction to a patient due to AMD loss of vision and positioning mechanism for an intraocular lens ) 是由 易虹 殷蔚 于 2019-09-11 设计创作，主要内容包括：本发明提供了用于设计因AMD丧失视力而为患者提供视力矫正的眼内透镜的方法,基于天然人眼光学特性和像差特性的眼球光学模型,包括前表面和后表面均为非球面的角膜、相对于眼睛的对称轴倾斜的视轴、偏心入射光瞳的偏心虹膜,在眼球的囊袋内植入双面非球面的天然人工晶体模型；再在眼球内植入至少一个非球面的眼内透镜；所述眼内透镜位于模型眼内的虹膜和囊袋之间并定位于睫状沟；眼内透镜、角膜、天然人工晶体模型形成同轴光学系统；眼内透镜紧贴虹膜之后,且眼内透镜的口径与缩小状态时虹膜直径匹配。(The invention provides a method for designing an intraocular lens for providing vision correction for a patient due to AMD loss of vision, based on an eyeball optical model of natural human eye optical characteristics and aberration characteristics, comprising a cornea with an aspheric front surface and a back surface, a visual axis inclined relative to the symmetry axis of the eye, an eccentric iris of an eccentric entrance pupil, and a natural intraocular lens model with a double-sided aspheric surface implanted in a capsular bag of the eyeball; implanting at least one aspheric intraocular lens into the eyeball; the intraocular lens is positioned between the iris and the capsular bag in the model eye and positioned in the ciliary sulcus; the intraocular lens, the cornea and the natural artificial lens model form a coaxial optical system; the intraocular lens is closely attached to the back of the iris, and the caliber of the intraocular lens is matched with the diameter of the iris in a reduced state.)

1. A method for designing an intraocular lens for providing vision correction to a patient for AMD loss of vision, an optical model of the eyeball based on the optical properties and aberration properties of the natural human eye, comprising a cornea with both its anterior and posterior surfaces being aspheric, a visual axis tilted with respect to the axis of symmetry of the eye, an eccentric iris with an eccentric entrance pupil, a natural intraocular lens model in the capsular bag of the eyeball; the method is characterized in that:

implanting at least one aspheric intraocular lens into the eyeball; the intraocular lens is positioned between the iris and the capsular bag in the eye and positioned in the ciliary sulcus; the intraocular lens, the cornea and the natural artificial lens model form a coaxial optical system; the intraocular lens is tightly attached to the iris, and the caliber of the intraocular lens is matched with the diameter of the iris in a reduced state;

the patient observes the target in a close distance, the iris shrinks, the light passes through the shrunk iris, the diopter of the imaging light beam is obtained through light path simulation calculation and is larger than the diopter of the imaging light beam which is not implanted into the intraocular lens, so that the imaging magnification of the coaxial optical system formed by the intraocular lens, the cornea in the eye and the natural intraocular lens model in the capsular bag is increased;

the patient observes the target in a long distance, the iris expands, the light passes through the expanded iris, the light in the edge area directly enters the natural artificial lens model in the capsular bag, and the iris and the natural artificial lens model form an imaging system;

the patient observes the target at a long distance, the iris expands, light passes through the expanded iris, the central imaging light beam is divergently transmitted to the retina after passing through an imaging surface between the natural artificial lens model and the retina, background spots with brightness are formed, and no actual image exists.

2. The method of claim 1 for designing an intraocular lens for providing vision correction to a patient for the loss of vision from AMD, wherein: the light-passing diameter of the intraocular lens is 0.8-1.5 mm.

3. The method of claim 2 for designing an intraocular lens for providing vision correction to a patient for the loss of vision from AMD, wherein: the light passing diameter of the intraocular lens is 1-1.2 mm.

4. The method of claim 1 for designing an intraocular lens for providing vision correction to a patient for the loss of vision from AMD, wherein: the front optical surface of the intraocular lens is spherical or aspherical; the back optical surface of the intraocular lens is spherical or aspherical.

5. The method of claim 1 for designing an intraocular lens for providing vision correction to a patient for the loss of vision from AMD, wherein: the diopter ranges from 2D to 10D.

6. The method of designing an intraocular lens for providing vision correction to a patient for the loss of vision in AMD, as claimed in any one of claims 1-5, wherein: the lens type of the intraocular lens is any one of three positive lens forms of double convex, single convex and positive meniscus.

7. A positioning mechanism for holding an intraocular lens according to claims 1 to 6, characterized in that: the supporting body is internally provided with an effective optical area for installing the intraocular lens, a fixing structure for reinforcing the intraocular lens and a hollow area for flowing aqueous humor in front and back of the eye.

8. The positioning mechanism of claim 7, wherein: the support main body comprises a first support main body, three first support climbers are arranged on the periphery of the first support main body, the first support main body is of a first hollow circular ring structure, the effective optical area is positioned at the center of the first hollow circular ring, and the intraocular lens is positioned at the center of the first hollow circular ring when the intraocular lens is used; the reinforcing structure comprises three first ribs which are arranged around the periphery of the intraocular lens at equal intervals and are connected with the inner side of the first hollow circular ring; a hollow area for the flow of front and back aqueous humor in the eye is arranged between the adjacent first ribs.

9. The positioning mechanism of claim 7, wherein: the supporting main body comprises a second supporting main body, three second supporting climbers are arranged on the periphery of the second supporting main body, a through hole matched with the size of the intraocular lens is formed in the center position in the second supporting main body, and the through hole is an effective optical area; when in use, the intraocular lens is embedded into the through hole and is reinforced by the second support main body, and a plurality of through grooves for flowing front and back aqueous humor in the eye are arranged on the periphery of the intraocular lens on the second support main body at intervals.

10. The positioning mechanism of claim 7, wherein: the support main body comprises a third support main body, the third support main body is of a square structure, third support climbers are arranged at four corners of the periphery of the third support main body respectively, the third support main body is of a third hollow circular structure, the effective optical area is positioned at the center of a third hollow circular ring, and the intraocular lens is positioned at the center of the third hollow circular ring when the intraocular lens is used; the reinforcing structure comprises four third ribs which are arranged at intervals around the periphery of the intraocular lens and are connected with the inner side of a third hollow circular ring of the third support main body; and hollow areas for the front and back aqueous humor to flow are formed between the third ribs positioned in the third hollow circular ring.

Technical Field

The invention relates to the technical field of intraocular lenses, in particular to an intraocular lens design method and a positioning mechanism of the intraocular lens.

Background

Age related macular degeneration (AMD) is a disease that affects the central macular area of the retina, causing the elderly to lose vision in the central field, while peripheral vision in the patient is often unaffected, thus maintaining the ability to distinguish direction early, while most patients lose reading ability late in the disease.

To address age related macular degeneration (AMD) technologies, a number of different technologies have been devised, some systems rely on magnifying the image, however this approach requires sacrificing the field of view. Such as an implanted telescopic system, has not been popularized for a long time because this approach reduces the visual angle of the human eye, the post-operative adaptation time is extremely long, the implantation is complicated, and the implantation is not suitable for a monocular patient.

Another prior art adopts a transposition technique, combines the non-coaxial offset of a convex surface and a concave surface, thereby transferring the light direction and converging a focus on the peripheral area of a fovea maculata center; the focus is shifted to the peripheral region of the fovea, and the apparent cell density of these regions is very low, depending on the particular condition of the patient's fundus, so that the range of patients to whom this technique is applied is limited.

Furthermore, approximately 80% of patients with AMD have undergone cataract surgery, i.e., intraocular lenses have been placed in the capsular bag of the eye. Intraocular lenses that have been implanted into the capsular bag are retained during cataract surgery, and no solution for such patients has been proposed, nor has there been a solution for improving reading vision.

Disclosure of Invention

In view of the deficiencies of the prior art, the present invention provides a simple, cost-effective method for designing intraocular lenses for use in improving the reading ability of patients with AMD, particularly patients who have been implanted with intraocular lenses.

In order to achieve the purpose, the invention adopts the following technical scheme:

a method for designing an intraocular lens for providing vision correction to a patient due to AMD loss of vision, an optical model of an eyeball based on optical characteristics and aberration characteristics of a natural human eye, including a cornea whose front and back surfaces are both aspherical, a visual axis inclined with respect to an axis of symmetry of the eye, an eccentric iris of an eccentric entrance pupil, a natural intraocular lens model having a double-sided aspherical surface implanted in a capsular bag of the eyeball;

implanting at least one aspheric intraocular lens into the eyeball; the intraocular lens is positioned between the iris and the capsular bag in the model eye and positioned in the ciliary sulcus; the intraocular lens, the cornea and the natural artificial lens model form a coaxial optical system; the intraocular lens is tightly attached to the iris, and the caliber of the intraocular lens is matched with the diameter of the iris in a reduced state;

the patient observes the target in a close distance, the iris shrinks, the light passes through the shrunk iris, the diopter of the imaging light beam is obtained through light path simulation calculation and is larger than the diopter of the imaging light beam which is not implanted into the intraocular lens, so that the imaging magnification of the coaxial optical system formed by the intraocular lens, the cornea in the eye and the natural intraocular lens model in the capsular bag is increased;

the patient observes the target in a long distance, the iris expands, the light passes through the expanded iris, the light in the edge area directly enters the natural artificial lens model in the capsular bag, and the iris and the natural artificial lens model form an imaging system;

the patient observes the target at a long distance, the iris expands, light passes through the expanded iris, the central imaging light beam is divergently transmitted to the retina after passing through an imaging surface between the natural artificial lens model and the retina, background spots with brightness are formed, and no actual image exists.

Wherein, its characterized in that: the light-passing diameter of the intraocular lens is 0.8-1.5 mm.

Preferably, the light-passing diameter of the intraocular lens is 1 to 1.2 mm.

Preferably, the anterior optical surface of the intraocular lens is spherical or aspherical.

Preferably, the posterior optical surface of the intraocular lens is spherical or aspherical.

Preferably, the lens shape of the intraocular lens is any one of three positive lens forms of double convex, single convex and positive meniscus.

The invention also provides a positioning mechanism for fixing the intraocular lens, which comprises an irregular polygonal supporting main body, wherein a plurality of supporting climbers extend from the periphery of the supporting main body, and an effective optical area for installing the intraocular lens, a fixing structure for reinforcing the intraocular lens and a hollow-out area for allowing front and back aqueous humor in the eye to flow are arranged in the supporting main body.

Furthermore, the support main body comprises a first support main body, three first support climbers are arranged on the periphery of the first support main body, the first support main body is of a first hollow circular ring structure, the effective optical area is positioned at the center of the first hollow circular ring, and the intraocular lens is positioned at the center of the first hollow circular ring when in use; the reinforcing structure comprises three first ribs which are arranged around the periphery of the intraocular lens at equal intervals and are connected with the inner side of the first hollow circular ring; a hollow area for the flow of front and back aqueous humor in the eye is arranged between the adjacent first ribs.

Furthermore, the support main body comprises a second support main body, three second support climbers are arranged on the periphery of the second support main body, a through hole matched with the size of the intraocular lens is formed in the center position in the second support main body, and the through hole is an effective optical area; when in use, the intraocular lens is embedded into the through hole and is reinforced by the second support main body, and a plurality of through grooves for flowing front and back aqueous humor in the eye are arranged on the periphery of the intraocular lens on the second support main body at intervals.

Furthermore, the support main body comprises a third support main body, the third support main body is of a square structure, third support climbers are respectively arranged at four corners of the periphery of the third support main body, the third support main body is of a third hollow circular ring structure, the effective optical area is positioned at the center of the third hollow circular ring, and the intraocular lens is positioned at the center of the third hollow circular ring when in use; the reinforcing structure comprises four third ribs which are arranged at intervals around the periphery of the intraocular lens and are connected with the inner side of a third hollow circular ring of the third support main body; and hollow areas for the front and back aqueous humor to flow are formed between the third ribs positioned in the third hollow circular ring.

Compared with the prior art, the invention has the following beneficial effects:

1. the invention aims at the patients who have implanted the artificial lens model in the capsular bag, and then implants the intraocular lens in the eye, and is positioned between the iris and the capsular bag and positioned in the ciliary sulcus; the cornea and the artificial lens model in the capsular bag form a coaxial optical system, the patient closely observes a target, the iris shrinks, and the diopter of the optical system is larger than that before the intraocular lens is not implanted. Due to the increase of the total diopter of the eyeball after the intraocular lens is implanted, the object distance of the near vision point is reduced, and the imaging magnification is increased, so that the reading vision of an AMD patient is improved.

2. The invention solves the problem of improving the vision during short-distance observation by improving the magnification, does not influence the far vision refractive parameters of AMD patients, keeps the visual angle and the magnification of natural eyes, and greatly reduces the inconvenience caused by narrow visual field and long adaptation period after operation brought by the prior technical proposal. The original direction resolution is kept while the reading vision of the patient is improved, and the long-range observation experience is achieved.

Drawings

FIG. 1 is a schematic view of the present invention viewed from a close distance;

FIG. 2 is a graph of the visual effect of the present invention with two times magnification;

FIG. 3 is a graph of intraocular lens power addition versus near point of view object distance (PO) for the present invention;

FIG. 4 is a graph of the power of the intraocular lens power increment versus power in accordance with the present invention;

FIG. 5 is a schematic view of the invention viewed from a distance;

FIG. 6 shows the energy ratio of the central imaging beam D to the peripheral beam D according to the present invention;

FIG. 7 is a diagram of an optical model of an eyeball according to the present invention;

FIG. 8 is a diagram illustrating optical path simulation in an embodiment of the present invention;

FIG. 9 is a graph of the MTF of the optical transfer function at a near 0 degree viewing angle according to the present invention;

FIG. 10 is an optical transfer function image at a near 5 degree viewing angle according to the present invention.

FIG. 11 is a schematic view of the positioning mechanism of the present invention;

FIG. 12 is a schematic structural view of another embodiment of the positioning mechanism of the present invention;

FIG. 13 is another schematic view of the structure of FIG. 12;

fig. 14 is a schematic structural diagram of another embodiment of the positioning mechanism of the present invention.

In the figure: cornea 1, intraocular lens 2, natural intraocular lens model 3, iris 4, sulcus 5, capsular bag 6, peripheral region 2A, anterior surface 11, posterior surface 12, visual axis 15, axis of symmetry 16, biaspheric intraocular lens 21, single aspheric natural intraocular lens model 22, first support body 31, first hollow annular structure 32, first ribs 33, first support flaps 34, second support body 41, through grooves 42, second support flaps 43, circular through holes 44, third support body 51, third hollow annular structure 52, third ribs 53, third support flaps 54.

Detailed Description

The technical solution of the present invention is further explained with reference to the drawings and the embodiments.

The present invention proposes a method for designing an intraocular lens for providing vision correction to a patient due to AMD loss of vision, based on a precise optical model of the eye of the natural human eye of optical characteristics and aberration characteristics, comprising a cornea 1 with both anterior 11 and posterior 12 surfaces being aspheric, a visual axis 15 inclined with respect to the axis of symmetry 16 of the eye, an eccentric iris 4 with an eccentric entrance pupil, a natural intraocular lens model 3 with a double aspheric surface implanted in the capsular bag 6 of the eye; the iris 4 is eccentric 0.5mm in the direction close to the nose. Then at least one aspheric intraocular lens 2 is implanted in the eyeball; the intraocular lens 2 is positioned between the iris 4 and the capsular bag 6 in the eye and positioned in the ciliary sulcus 5; the intraocular lens 2, the cornea 1 and the natural artificial lens model 3 form a coaxial optical system; the intraocular lens 2 is closely attached to the iris 4, and the diameter of the intraocular lens 2 is matched to the diameter of the iris 4 in the contracted state. Intraocular lens 2 is preferably located in the posterior chamber of the eye, and if an intraocular lens 2 is to be implanted into the anterior chamber, the range of patients who are ill-fitting is large, such as glaucoma. Also unsuitable are superficial anterior chamber, iris 4 depigmentation, iris 4 atrophy, deformity, corneal 1 endothelial dystrophy, etc., as well as aesthetic considerations.

In conjunction with fig. 1, point P is a close-range target viewpoint, the distance being suitable for viewing item details and reading text. When the details of the articles are observed in a close range and books are read, sufficient lighting light can be ensured; meanwhile, when the object is close, the pupil (iris 4) is contracted from a relaxed state to a contracted state, and the diameter after the contraction is 1.5mm at least. The light emitted from the point P passes through the pupil in the contraction state, and the aperture of the imaging light beam is limited. After the intraocular lens 2 is tightly attached to the iris 4, and the caliber of the intraocular lens 2 is matched with the diameter of the iris 4 in the shrinking state, the refraction effect of the imaging light beam in the small pupil state is ensured, and the influence of the imaging light beam on the telephoto refraction is reduced in the pupil expanding state. In the case of near vision, the beam of the intraocular lens 2 is imaged at the point P' of the retina by the intraocular lens located in the capsular bag 6. The intraocular lens 2, the cornea 1 in the eye, and the natural intraocular lens model 3 in the capsular bag 6 form a coaxial optical system. When a patient observes a target in a close distance, the iris 4 contracts (the pupil becomes smaller), light passes through the contracted iris 4, and the diopter of the imaging light beam is calculated through light path simulation and is larger than the diopter of the imaging light beam which is not implanted into the intraocular lens 2 and is 2-10D; as the total diopter of the eyeball is increased after the intraocular lens 2 is implanted, the object distance (spacing, wherein O represents the vertex of the cornea 1) of the near vision point is reduced, so that the imaging magnification of the coaxial optical system formed by the intraocular lens 2, the cornea 1 in the eye and the natural artificial lens model 3 in the capsular bag 6 is increased, and the reading vision of the AMD patient is improved. The effect of the magnification on the viewing angle is shown in fig. 2.

As shown in fig. 3, through the optical path simulation calculation, the diopter increase of the intraocular lens 2 is related to the near vision object distance (PO) as shown in fig. 3, and when the diopter increment introduced by the intraocular lens 2 reaches 6D, the near vision point distance is reduced to 100 mm. When the diopter increment of the intraocular lens 2 reaches 10D, the myopic point distance (observation distance, distance from the book to the vertex of the cornea 1) is reduced to about 70 mm. Meanwhile, the relationship curve of the 2 diopter increment and the magnification of the intraocular lens is calculated by the optical path and is shown in figure 4: when the intraocular lens 2 of the present disclosure is introduced to a diopter increment of up to 6 diopters, a magnification of approximately 2.5 diopters without the intraocular lens 2, has been found to substantially improve the reading vision of AMD patients. Based on the above computational analysis, the proposed diopter increments for the intraocular lens 2 embodiment of the present invention are preferably in the range of 4-8D, and can be relaxed to 2-10D for special cases. Comfortable near viewing and magnification have been achieved.

Referring to fig. 5, the invention improves the vision improvement in close-range observation without affecting the far vision refractive parameters of the AMD patient, retains the visual angle and magnification of the natural eye, and greatly reduces the inconvenience caused by narrow visual field and long adaptation period after operation. The original direction resolution is kept while the reading vision of the patient is improved, and the long-range observation experience is achieved.

The patient observes the target in a long distance, the iris 4 expands, the light passes through the expanded iris 4, the light in the edge area directly enters the natural artificial lens model 3 in the capsular bag 6, and the iris 4 and the natural artificial lens model 3 form an imaging system; when the observation target is far away, the pupil (iris 4) will expand to ensure the light input amount because the received object reflects light or emits light less. The diameter D (entrance pupil size) of the imaging beam exceeds the diameter D of the optically effective area of the intraocular lens 2 disclosed in the present invention, and the peripheral area light passes through the peripheral area 2A having no refractive power and is directly incident on the natural intraocular lens model 3 in the capsular bag 6. Only cornea 1 and artificial lens participate in the edge beam imaging, the intraocular lens 2 does not interfere with the edge beam imaging, and the imaging visual angle and magnification of the edge beam are not influenced by the intraocular lens 2

The patient observes the target at a long distance, iris 4 expands, light passes through the expanded iris 4, the central imaging light beam is diverged and spread to the retina after passing through an imaging surface between the natural artificial lens model 3 and the retina, background spots with brightness are formed, and no actual image exists. For the imaging condition of the central imaging light beam, namely the aperture d range, because the observation target is far and the object distance is increased, the imaging surface passing through the intraocular lens 2 is positioned between the intraocular lens model and the retina, the light beam after passing through the image surface is dispersed and spread to the retina to become a background bright spot with certain brightness, and no actual image exists. The optical diameter of the intraocular lens 2 can be customized (pupil size when reading by patient). Wherein the light passing diameter of the intraocular lens 2 is 0.8-1.5mm, preferably 1-1.2 mm. The preferred clear diameter of the disclosed intraocular lens 2 is 1-1.2mm, the energy ratio of the central imaging beam D to the peripheral beam D is shown in fig. 6, and when the preferred clear diameter of the intraocular lens 2 is 1mm, the energy of the peripheral beam (D-D) will increase from 1.2 times to 8 times of the central beam D as the diameter of the pupil increases from 1.5mm to 3 mm. Therefore, the far distance marginal beam imaging will be dominant, and the processing of the image by the optic nerves and brain will focus on identifying the real image formed by the marginal beam (D-D) and neglecting the diffuse spot at the center D, so the field of view and magnification of the AMD patient when viewing the long distance view will be the same as before implanting the intraocular lens 2.

The intraocular lens 2 disclosed in the present invention has a diopter ranging from 2 to 10D, preferably from 5 to 8D; the effective diameter of light passing is 0.8-1.5mm, preferably 1-1.2 mm. Comprising two optical surfaces, a front optical surface, which may be spherical or aspherical, and a rear optical surface, which may be spherical or aspherical, 12. The lens type of the intraocular lens 2 is any one of three positive lens forms of double convex, single convex and positive meniscus. The expression of the aspherical surface is as follows:

wherein: x: face vector height coordinate values (optical axis direction); y: lens caliber (perpendicular to optical axis radius direction); c: a radius of curvature of the substrate; k: a conic constant; an: coefficient of the n-th order term.

The design of the novel intraocular lens 2 disclosed by the invention takes into account the optical characteristics and aberration characteristics of the human eye, such as the inclination of the visual axis 15 and the pupil deviation, based on a precise eyeball optical model. As shown in fig. 7: the eye model comprises a cornea 1 with both anterior surface 11 and posterior surface 12 being aspheric, including 0.5mm decentration of the pupil in the nasal direction, including an inclination of the visual axis 15 with respect to the axis of symmetry 16 of the eyeball, including a double-sided aspheric natural lens model.

The human eye precision optical model on which the novel intraocular lens 2 disclosed in the present invention was designed is represented by the lower surface list (table 1):

TABLE 1

Using the disclosed method, a 10D double-sided aspherical intraocular lens 2 was designed, examples of which are shown in table 2:

surface of	R value	Value of K	A2	A4	A6	A8
							Front side	4.81	11.187	0	-0.002090735	-0.010236057	0
Rear end	7.02	23.094	0	-0.00122843	-0.004508297	0

TABLE 2

The above table shows the design of an intraocular lens 2 of the meniscus type, with both the front and back surfaces 12 being aspheric (or designed as a single aspheric surface) according to the method disclosed herein. The intraocular lens 2 was matched with a single aspheric 22D intraocular lens of the type shown in table 3, whose optical path was simulated as in fig. 8, and the 10D double aspheric intraocular lens 212 shown in the above table was imaged under a small pupil together with the single aspheric intraocular lens and the cornea 1, to reduce the closest observation distance and at the same time increase the magnification. Thereby improving the reading vision of AMD patients. Fig. 9 shows the MTF curve of the optical transfer function at a near 0 degree viewing angle, which shows the imaging quality. Fig. 10 shows an optical transfer function image at a near 5 degree viewing angle.

Surface of	R value	Value of K	A2	A4	A6	A8
							Front side	7.1497	0	0	0	0	0
Rear end	-36.3903	0	-0.0068159	0.0010213	-6.21E-05	0

TABLE 3

Referring to fig. 11-14, an intraocular lens 2 is disclosed for positioning in the ciliary sulcus 5 of a human eye. The implant region is located very close to the pupil and in the design of the structure, consideration is given to reducing the risk of pupillary clamping while avoiding aqueous exchange that blocks both the anterior and posterior chamber. Therefore, the invention also provides a positioning mechanism for fixing the intraocular lens 2, which comprises an irregular polygonal supporting main body, wherein a plurality of supporting climbers extend from the periphery of the supporting main body, and an effective optical area for installing the intraocular lens 2, a fixing structure for reinforcing the intraocular lens 2 and a hollow area for flowing aqueous humor in front of and behind the eye are arranged in the supporting main body. The positioning stability of the intraocular lens 2 is ensured, the pupil clamping is avoided, and the effective optical area of the intraocular lens 2 is connected with the supporting outer frame of the intraocular lens 2 through ribs, so that a hollow structure is formed on the intraocular lens 2, and the aqueous humor exchange of the anterior chamber and the posterior chamber is facilitated.

The support main body comprises a first support main body 31, three first support climbers 34 are arranged on the periphery of the first support main body 31, the first support main body 31 is a first hollow circular ring-shaped structure 32, the effective optical area is positioned at the center of the first hollow circular ring, and the intraocular lens 2 is positioned at the center of the first hollow circular ring when in use; the reinforcing structure comprises three first ribs 33, the three first ribs 33 are arranged around the periphery of the intraocular lens 2 at equal intervals and are connected with the inner side of the first hollow circular ring; hollow areas for the flow of front and back aqueous humor in the eye are arranged between the adjacent first ribs 33.

Furthermore, the support body includes a second support body 41, three second support flaps 43 are provided on the periphery of the second support body 41, a through hole matching the size of the intraocular lens 2 is provided at the center position in the second support body 41, and the through hole is an effective optical zone; in use, the intraocular lens 2 is inserted into the through-hole and reinforced by the second support body 41, and a plurality of through grooves 42 for allowing the flow of aqueous humor anteroposteriorly and posteriorly in the eye are spaced apart from the outer periphery of the intraocular lens 2 on the second support body 41. The through slots 42 may be in a fan configuration or a circular through hole 44 configuration.

The first supporting flap 34 and the second supporting flap 43 are in a hook-shaped structure, and the openings of the hook-shaped supporting flaps are oriented in the same direction after the arrangement and are synchronously arranged clockwise/anticlockwise.

The supporting body comprises a third supporting body 51, the third supporting body 51 is of a square structure, the four corners of the periphery of the third supporting body are respectively provided with a third supporting climbing 54, the third supporting body 51 is of a third hollow circular ring-shaped structure 52, the effective optical area is positioned at the center of the third hollow circular ring, and the intraocular lens 2 is positioned at the center of the third hollow circular ring when in use; the reinforcing structure includes four third ribs 53, the four third ribs 53 being provided at intervals around the periphery of the intraocular lens 2 and connected to the inside of the third hollow ring of the third support body 51; hollow areas for the flow of the front and back aqueous humor in the eye are formed between the third ribs 53 positioned in the third hollow circular ring. Four independent third supporting climbers are distributed on the periphery of the third supporting main body to strengthen the positioning stability of the intraocular lens 2 in the ciliary sulcus 5, and the third supporting climbers 54 are of annular structures.

Finally, the above embodiments are only for illustrating the technical solutions of the present invention and not for limiting, although the present invention has been described in detail with reference to the preferred embodiments, it should be understood by those skilled in the art that modifications or equivalent substitutions may be made to the technical solutions of the present invention without departing from the spirit and scope of the technical solutions of the present invention, and all of them should be covered in the claims of the present invention.