Eyeball three-dimensional model construction method and macular buckle surgery navigation system

Abstract

The invention relates to the technical field of operation guidance, and discloses an eyeball three-dimensional model construction method and a macular buckle operation navigation system.The method comprises the following steps that S1, data extraction of all parts of an eyeball is conducted, specifically, S11, cornea parameter establishment and variability analysis are conducted; s12, establishing parameters of the front half part of the eyeball and carrying out variability analysis; s13, parameter establishment and variability analysis of the rear half part of the eyeball; s2, constructing an eyeball three-dimensional model through the cornea parameters, the eyeball front half part parameters and the eyeball rear half part parameters. The system is matched with the method. According to the method, the difficulty of eyeball three-dimensional reconstruction is effectively reduced, the macular positioning precision is greatly improved, the operation time is shortened, the difficulty of a macular buckle operation is reduced, and individualized accurate implementation of the macular buckle operation is realized.

Description

Technical Field

[0001] The present application relates to the technical field of surgical guidance, and specifically to a method for constructing a three-dimensional model of an eyeball and a macular buckle surgery navigation system. Background Art

[0002] In 2020, there are 2.5 billion myopic patients in the world, and 600 million patients with high myopia, of which about 60 million have traction maculopathy that requires surgical intervention. Among the 170 million people with high myopia in China, about 12 million have traction maculopathy. High myopia traction maculopathy is caused by the continuous growth of the axial length of the eye of patients with high myopia, the irregular expansion of the eyeball backwards, which causes traction on the retina and leads to macular degeneration. It may cause patients to have a continuous decline in vision and even the risk of blindness. It is a difficult problem in clinical treatment and a hot spot and difficulty in global ophthalmology research.

[0003] Studies have shown that macular buckling surgery has good efficacy and safety in the treatment of high myopic traction maculopathy, bringing new hope to patients with high myopic traction maculopathy. However, due to technical difficulties, the awareness and popularity of macular buckling surgery are still quite different from those abroad. The posterior part of the eyeball of patients with high myopic traction maculopathy often expands irregularly backwards, and the length of the eyeball also has a large variability, which makes it impossible to use a unified paradigm for surgery. Individualized surgical design has become a rigid demand. Before surgery, it is necessary to design the expected macular area pad height and select the corresponding buckling implant size based on factors such as the patient's eyeball morphology and axial length. At the same time, due to the blind spots in the surgical operation, the relative position of the buckling implant and the important structure of the macular area cannot be fully exposed during the operation, so the precise positioning of the buckling implant during the operation increases the difficulty of the operation. In order to reduce the difficulty of macular buckling surgery, improve surgical safety and implement individualized treatment strategies, accurate surgical navigation systems play a vital role in simplifying surgical methods.

[0004] The traditional navigation method for macular buckling surgery is to use MRI to reconstruct the entire eyeball in three dimensions to build a three-dimensional model of the eyeball, helping clinicians understand the patient's eye shape before surgery. However, due to the limitation of MRI imaging resolution, only the shape of the eyeball can be obtained, and the position of the fovea cannot be accurately located on the three-dimensional image. At the same time, MRI examinations are expensive and require professional technicians to perform three-dimensional modeling after sampling. The economic benefits of MRI navigation are relatively low. Therefore, there is an urgent need for an accurate and simplified surgical navigation system in clinical practice to help clinicians complete macular buckling surgery more safely and effectively. Summary of the invention

[0005] The purpose of this application is to provide a method for constructing a three-dimensional model of the eyeball and a macular buckle surgery navigation system to solve the technical problems raised in the above background.

[0006] To achieve the above objectives, this application discloses the following technical solutions:

[0007] In a first aspect, the present application discloses a method for constructing a three-dimensional model of an eyeball, the method comprising the following steps:

[0008] S1- Extraction of data from various parts of the eyeball, including:

[0009] S11-Establishment of corneal parameters and analysis of variability;

[0010] S12-Establishment of parameters and variability analysis of the anterior half of the eyeball;

[0011] S13-Establishment of parameters and variability analysis of the posterior half of the eyeball;

[0012] S2-Construct a three-dimensional eyeball model through corneal parameters, anterior half of the eyeball parameters and posterior half of the eyeball parameters.

[0013] Preferably, the corneal parameter establishment and variability analysis specifically include:

[0014] Based on the anterior segment OCT technology, the corneal diameter AB was obtained with the limbus as the measurement point;

[0015] Corneal variability analysis was performed based on the obtained corneal diameter.

[0016] Preferably, the establishment of parameters of the front half of the eyeball and the analysis of variability specifically include:

[0017] Based on MRI technology, the parameters of the front half of the eyeball are measured with the eyeball equatorial plane as the boundary, wherein the parameters of the front half of the eyeball include the transverse diameter CD of the eyeball passing through the eyeball equatorial plane and the vertical distance OO' from the vertex of the anterior surface of the cornea to the eyeball equatorial plane;

[0018] The variability analysis of the anterior half of the eye was performed based on the transverse diameter of the eye passing through the equatorial plane of the eye and the vertical distance between the vertex of the anterior corneal surface and the equatorial plane of the eye.

[0019] Preferably, the establishment of parameters of the posterior half of the eyeball and the analysis of variability specifically include:

[0020] Based on the wide-angle posterior segment OCT technology, the parameters of the posterior half of the eyeball are measured with the posterior equatorial plane of the eyeball as the reference, and the parameters of the posterior half of the eyeball include the vertical distance O'M from the vertex of the macula center of the posterior sclera to the equatorial plane of the eyeball;

[0021] The variability analysis of the posterior half of the eye was performed based on the vertical distance between the central vertex of the posterior scleral macula and the ocular equatorial plane.

[0022] Preferably, the three-dimensional eyeball model is constructed by using corneal parameters, anterior half of the eyeball parameters and posterior half of the eyeball parameters, specifically including:

[0023] S21-Acquire the corneal curvature R and the anterior scleral curvature R' based on IOLMaster;

[0024] S22-constructing a corneal model OAB based on the corneal curvature R and the corneal diameter AB, wherein the corneal model OAB includes point O, point A, point B and a plurality of connecting lines; wherein point O is the vertex of the anterior surface of the cornea, point A and point B are points on the corneal margin corresponding to the corneal diameter, and point A and point B are located on both sides of point O respectively;

[0025] S23-constructing the anterior half eyeball model OACO'DB based on the anterior half scleral curvature R', the eyeball transverse diameter CD passing through the eyeball equatorial plane, the vertical distance OO' between the vertex of the anterior surface of the cornea and the eyeball equatorial plane, and the corneal model OAB, wherein the anterior half eyeball model OACDB includes point O, point A, point B, point C, point O', point D, and a number of connecting lines, wherein point O' is the intersection of the vertical line passing through point O on the eyeball equator and the eyeball equator, point C and point D are two points on the eyeball equator corresponding to the eyeball transverse diameter passing through the eyeball equatorial plane, and point C and point D are located on both sides of point O respectively;

[0026] S24-Acquire the axial length OM of the eyeball based on the IOLMaster, and determine the position of the posterior scleral macula center vertex M based on the axial length OM and the extension line of the line connecting the points O and O', wherein the posterior scleral macula center vertex M is located on the extension line of the line connecting the points O and O';

[0027] S25: Based on the position of the central vertex M of the posterior scleral macula and the model of the front half of the eyeball OACO'DB, a three-dimensional model of the eyeball is constructed, and the area formed by points O, A, C, D and B in the three-dimensional model of the eyeball is defined as a constant area with small variability, and the area formed by point C, the central vertex M of the posterior scleral macula and point D in the three-dimensional model of the eyeball is defined as a variable area with large variability.

[0028] In a second aspect, the present application discloses a macular buckle surgery navigation system, including a model building module and a buckle suture point calculation module;

[0029] The model building module is configured as follows: accurately calculating the axial length of the eye through IOLMaster, determining the location of the fovea, evaluating the amount of macular splitting based on OCT, and estimating the amount of surgery;

[0030] The cingulum suture point calculation module is configured to calculate the positions of the cingulum suture points P1 and P2 based on the three-dimensional model of the eyeball.

[0031] Preferably, the buckle suture points P1 and P2 are respectively located beside the superior rectus muscle and the lateral rectus muscle in the superior temporal quadrant, and are located in the constant area; wherein, the buckle suture points P1 and P2 are determined based on the planned shortened axial length MM' and the distance between the buckle top pressure center and the terminal fixing ring, wherein the axial length MM' is the distance between the position of the fovea and the shortened target fovea M', and the target fovea M' is located on the extension line of the vertical line between the apex of the anterior surface of the cornea and the equatorial plane of the eyeball.

[0032] Beneficial effects: Compared with the traditional technology that must rely on orbital MRI to build a model, the present invention uses multi-modal imaging equipment including MRI when building a model. In the final clinical application, the accurate simplified three-dimensional model of the eyeball can be built by relying on macular OCT scanning and axial measurement. The model building method is simpler and has considerable time and economic cost benefits. Secondly, OCT has a higher resolution than MRI, and can more accurately quantify structural abnormalities in the macular area, which is more suitable for individualized navigation design in macular buckling surgery. Further, in the application of clinical navigation, only the data of OCT and biometer are needed to build a simplified model to determine the position of the fovea, and the position of the corresponding buckling suture points P1 and P2 can be further determined. Traditional imaging equipment such as MRI or CT is abandoned, and the effect that can only be completed by ophthalmologists is achieved. It is simple and practical, greatly reducing the patient's additional testing costs and consultation time. At the same time, the navigation algorithm based on OCT has an inherent advantage in resolution, so the quantification is more accurate, which is more conducive to the promotion of macular buckling surgery. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present application. For those skilled in the art, other drawings can be obtained based on these drawings without paying any creative work.

[0034] Figure 1 A schematic diagram of a process for constructing a three-dimensional eye model provided in an embodiment of the present application;

[0035] Figure 2 A schematic cross-sectional view of a three-dimensional model of an eyeball provided in an embodiment of the present application;

[0036] Figure 3 A schematic diagram of corneal parameter measurement provided in an embodiment of the present application;

[0037] Figure 4A schematic diagram of measuring parameters of the front half of the eyeball provided in an embodiment of the present application;

[0038] Figure 5 A schematic diagram of measuring parameters of the back half of an eyeball provided in an embodiment of the present application;

[0039] Figure 6 A schematic diagram of a cross-section example of a simplified three-dimensional model of an eyeball provided in an embodiment of the present application;

[0040] Figure 7 A schematic diagram of a three-dimensional remodel of an eyeball and its cross-section provided in an embodiment of the present application. DETAILED DESCRIPTION

[0041] The technical solutions in the embodiments of the present application are described clearly and completely below. Obviously, the described embodiments are only part of the embodiments of the present application, not all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present application.

[0042] In this article, the term "comprising" is intended to cover non-exclusive inclusion, so that a process, method, article or device that includes a series of elements includes not only those elements, but also includes other elements not explicitly listed, or also includes elements inherent to such process, method, article or device. In the absence of more restrictions, the elements defined by the sentence "comprising..." do not exclude the presence of other identical elements in the process, method, article or device that includes the elements.

[0043] In a first aspect, this embodiment provides Figure 1 A method for constructing a three-dimensional eyeball model is shown, the method comprising the following steps:

[0044] S1- Extraction of data from various parts of the eyeball, including:

[0045] S11- Establishment of corneal parameters and analysis of variability, specifically:

[0046] Based on the anterior segment OCT technology, the corneal diameter AB was obtained with the limbus as the measurement point;

[0047] Corneal variability analysis was performed based on the obtained corneal diameter.

[0048] S12-Establishment of parameters and variability analysis of the front half of the eyeball, specifically:

[0049] Based on MRI technology, the parameters of the front half of the eyeball are measured with the eyeball equatorial plane as the boundary, wherein the parameters of the front half of the eyeball include the transverse diameter CD of the eyeball passing through the eyeball equatorial plane and the vertical distance OO' from the vertex of the anterior surface of the cornea to the eyeball equatorial plane;

[0050] The variability analysis of the anterior half of the eye was performed based on the transverse diameter of the eye passing through the equatorial plane of the eye and the vertical distance between the vertex of the anterior corneal surface and the equatorial plane of the eye.

[0051] S13-Establishment of parameters and variability analysis of the posterior half of the eyeball, specifically:

[0052] Based on the wide-angle posterior segment OCT technology, the parameters of the posterior half of the eyeball are measured with the posterior equatorial plane of the eyeball as the reference, and the parameters of the posterior half of the eyeball include the vertical distance O'M from the vertex of the macula center of the posterior sclera to the equatorial plane of the eyeball;

[0053] The variability analysis of the posterior half of the eye was performed based on the vertical distance between the central vertex of the posterior scleral macula and the ocular equatorial plane.

[0054] S2-Build the three-dimensional model of the eyeball through corneal parameters, parameters of the front half of the eyeball and parameters of the back half of the eyeball, including:

[0055] S21-Acquire the corneal curvature R and the anterior scleral curvature R' based on IOLMaster;

[0056] S22-constructing a corneal model OAB based on the corneal curvature R and the corneal diameter AB, wherein the corneal model OAB includes point O, point A, point B and a plurality of connecting lines; wherein point O is the vertex of the anterior surface of the cornea, point A and point B are points on the corneal margin corresponding to the corneal diameter, and point A and point B are located on both sides of point O respectively;

[0057] S23-constructing the anterior half eyeball model OACO'DB based on the anterior half scleral curvature R', the eyeball transverse diameter CD passing through the eyeball equatorial plane, the vertical distance OO' between the vertex of the anterior surface of the cornea and the eyeball equatorial plane, and the corneal model OAB, wherein the anterior half eyeball model OACDB includes point O, point A, point B, point C, point O', point D, and a number of connecting lines, wherein point O' is the intersection of the vertical line passing through point O on the eyeball equator and the eyeball equator, point C and point D are two points on the eyeball equator corresponding to the eyeball transverse diameter passing through the eyeball equatorial plane, and point C and point D are located on both sides of point O respectively;

[0058] S24-Acquire the axial length OM of the eyeball based on IOLMaster, and calculate the axial length OM and O point and O'

[0059] The extended line of the point connection determines the position of the posterior scleral macular center vertex M, wherein the posterior sclera

[0060] The vertices of the center of the macula, M, are located on the extension line of the line connecting points O and O';

[0061] S25: Based on the position of the central vertex M of the posterior scleral macula and the model of the front half of the eyeball OACO'DB, a three-dimensional model of the eyeball is constructed, and the area formed by points O, A, C, D and B in the three-dimensional model of the eyeball is defined as a constant area with small variability, and the area formed by point C, the central vertex M of the posterior scleral macula and point D in the three-dimensional model of the eyeball is defined as a variable area with large variability.

[0062] The constructed three-dimensional model of the eyeball is as follows Figure 2 shown.

[0063] In a second aspect, the present embodiment discloses a macular buckling surgery navigation system, including a model building module and a buckling suture point calculation module;

[0064] The model building module is configured as follows: accurately calculating the axial length of the eye through IOLMaster, determining the location of the fovea, evaluating the amount of macular splitting based on OCT, and estimating the amount of surgery;

[0065] The buckle suture point calculation module is configured to calculate the positions of buckle suture points P1 and P2 based on the three-dimensional model of the eyeball. The buckle suture points P1 and P2 are located beside the superior rectus muscle and the lateral rectus muscle in the superior temporal quadrant, respectively, and are located in the constant area; the buckle suture points P1 and P2 are determined based on the planned shortened axial length MM' and the distance between the buckle top pressure center and the terminal fixing ring, wherein the axial length MM' is the distance between the position of the fovea and the shortened target fovea M', and the target fovea M' is located on the extension of the vertical line between the vertex of the anterior surface of the cornea and the equatorial plane of the eyeball.

[0066] Below, this article further introduces the above technical content in detail based on actual test examples:

[0067] Firstly, ocular biological parameters were measured in 40 patients with high myopia based on MRI, anterior and posterior segment OCT, and biometer (IOL-master).

[0068] When establishing corneal parameters and analyzing their variability, Figure 3 As shown, the measured corneal diameter (with the corneal limbus as the measurement point) is 12.16±0.23 mm, and the corresponding variability analysis result is that the variability is small.

[0069] In the establishment of parameters and variability analysis of the anterior half of the eyeball, such as Figure 4As shown, the measured transverse diameter of the eyeball through the equatorial plane is 25.54±0.35mm, and the corresponding variability analysis result is that the variability is small. The measured vertical distance from the vertex of the anterior surface of the cornea to the equatorial plane is 13.68±0.27mm, and the corresponding variability analysis result is that the variability is small.

[0070] In the establishment of parameters and variability analysis of the posterior half of the eyeball, such as Figure 5 The measured vertical distance between the posterior scleral macula center vertex and the equatorial plane of the eyeball is 17.52±1.79mm, and the corresponding variability analysis results show that the variability is large; the posterior sclera morphology is highly variable, but the position of the macula center is located on the eye axis and remains basically unchanged; the amount of macular splitting is highly variable, and the amount of surgery varies greatly.

[0071] Through the analysis of multimodal biological parameters of 40 patients with high myopia, a simplified model of the eyeball with high myopia was constructed, providing a valuable geometric reference for surgical navigation. Figure 6 As shown, the structure of the eyeball in high myopia is divided into two areas: 1) OACDB, the front half of the eyeball, is a constant area with small 3D parameter variation; 2) CMD, the back half of the eyeball, is a variable area with large individual differences. The axial length of patients with high myopia varies greatly, but point M is still located on the extension line of OO'. The position of OM can be determined by accurately measuring the value of the axial length OM. Since the macular buckling needs to be fixed in the constant area, it is only necessary to determine the location of M to carry out accurate surgical positioning design before surgery. Therefore, this simplified eyeball model can meet the needs of buckling surgery navigation.

[0072] Furthermore, based on the construction of the simplified eyeball model, the positions of the cingulum suture points P1 and P2 are calculated.

[0073] refer to Figure 7 As shown in Figure 1, the cingulum suture points P1 and P2 are located next to the superior rectus and lateral rectus muscles in the superior temporal quadrant, respectively, and are located within the constant zone. The location of the P points (P1 and P2) is determined by the planned shortening of the axial length MM' and the distance between the cingulum top pressure center and the terminal fixation ring. Figure 7 In the figure, O is the vertex of the anterior surface of the cornea, M is the fovea (i.e., the aforementioned vertices of the posterior scleral macula), L is the limbus, ON is the optic nerve; OM is the axial length, M'M is the estimated apical pressure (i.e., the planned shortening of the axial length), the shaded part is the macular buckle, B is the position of the macular buckle pressure disk, P is the front suture point of the buckle, and LP is the distance from the buckle suture point to the limbus.

[0074] Therefore, in clinical practice, the size of the macular buckle can be determined according to the axial length OM.

[0075] And further determine the location of the cingulum suture points P1 and P2 to optimize the macular cingulum surgery process.

[0076] Based on the above, the eyeball three-dimensional model construction method and macular buckling surgery navigation system of this embodiment do not require the help of MRI, effectively reducing the difficulty of eyeball three-dimensional reconstruction, greatly improving the accuracy of macula positioning, shortening the operation time, reducing the difficulty of macular buckling surgery, and realizing the individualized and precise implementation of macular buckling surgery. This embodiment describes how to use multimodal imaging technology to construct a simplified three-dimensional eyeball model and related measurement parameters, and finally how to achieve the construction of a simplified eye model relying only on OCT and biometer. Different from the traditional technology that must rely on orbital MRI to build a model, the simplified eye model of this scheme only relies on multimodal imaging equipment including MRI in model exploration, and in the final clinical application, this scheme only relies on macular OCT scanning and axial measurement to complete the accurate construction of a simplified eye model. In actual operation, the model construction is simpler and has considerable time and economic cost-effectiveness; secondly, OCT has a higher resolution than MRI, can more accurately quantify structural abnormalities in the macular area, and is more suitable for individualized navigation design in macular buckling surgery.

[0077] This embodiment innovatively proposes a macular buckling surgery navigation algorithm developed based on a simplified eye model, which helps clinicians better perform surgical positioning and quantitative design of macular buckling. Through algorithm optimization, the navigation system of this solution also only needs OCT and biometer data to build. Since traditional imaging equipment such as MRI or CT is abandoned, the navigation design of this solution can be completely completed by ophthalmologists. The algorithm is simple and practical, which greatly reduces the patient's additional testing costs and consultation time. At the same time, the navigation algorithm based on OCT has an inherent advantage in resolution, so the quantification is more accurate. In practical applications, the navigation system of this solution is more effective and more feasible than traditional methods, which is more conducive to the promotion of macular buckling surgery.

[0078] In the specific implementation of clinical cases, this program fully verified the feasibility and accuracy of the macular buckling navigation system based on a simplified eye model, which is more accurate, faster and safer than traditional technologies. Under the guidance of this navigation system, 28 patients who underwent macular buckling surgery achieved very good expected results, which were manifested in precise positioning consistent with the preoperative design, greatly shortened operation time, and greatly reduced surgical operation difficulty, and all patients had no obvious complications.

[0079] In the embodiments provided in the present application, it should be understood that the embodiments described herein can be implemented in hardware, software, firmware, middleware, code or any appropriate combination thereof. For hardware implementation, the processor can be implemented in one or more of the following units: application specific integrated circuit ASIC, digital signal processor DSP, digital signal processing device DSPD, programmable logic device PLD, field programmable gate array FPGA, processor, controller, microcontroller, microprocessor, other electronic units designed to implement the functions described herein or their combination. For software implementation, part or all of the flow of the embodiment can be completed by instructing the relevant hardware through a computer program. When implemented, the above program can be stored in a computer-readable storage medium or transmitted as one or more instructions or codes on a computer-readable storage medium. Computer-readable storage media include computer storage media and communication media, wherein the communication medium includes any medium that is convenient for transmitting a computer program from one place to another. The storage medium can be any available medium that a computer can access. The computer-readable storage medium can include, but is not limited to, RAM, ROM, EEPROM, CD-ROM or other optical disk storage, disk storage medium or other magnetic storage device, or any other medium that can be used to carry or store the desired program code in the form of an instruction or data structure and can be accessed by a computer.

[0080] Finally, it should be noted that the above are only preferred embodiments of the present application and are not intended to limit the present application. Although the present application has been described in detail with reference to the aforementioned embodiments, it is still possible for those skilled in the art to modify the technical solutions described in the aforementioned embodiments, or to make equivalent substitutions for some of the technical features therein. Any modifications, equivalent substitutions, improvements, etc. made within the spirit and principles of the present application shall be included in the protection scope of the present application.

Claims

1. A method for constructing a three-dimensional model of an eyeball, characterized in that: The method comprises the following steps: S1- Extraction of data from various parts of the eyeball, including: S11-Establishment of corneal parameters and analysis of variability; S12-Establishment of parameters and variability analysis of the anterior half of the eyeball; S13-Establishment of parameters and variability analysis of the posterior half of the eyeball; S2-Construct a three-dimensional eyeball model through corneal parameters, anterior half of the eyeball parameters and posterior half of the eyeball parameters.

2. The method for constructing a three-dimensional eyeball model according to claim 1, characterized in that: The corneal parameter establishment and variability analysis specifically include: Based on the anterior segment OCT technology, the corneal diameter AB was obtained with the limbus as the measurement point; Corneal variability analysis was performed based on the obtained corneal diameter.

3. The method for constructing a three-dimensional eyeball model according to claim 2, characterized in that: The establishment of parameters of the front half of the eyeball and the analysis of variability specifically include: Based on MRI technology, the parameters of the front half of the eyeball are measured with the eyeball equatorial plane as the boundary, wherein the parameters of the front half of the eyeball include the transverse diameter CD of the eyeball passing through the eyeball equatorial plane and the vertical distance OO' from the vertex of the anterior surface of the cornea to the eyeball equatorial plane; The variability analysis of the anterior half of the eye was performed based on the transverse diameter of the eye passing through the equatorial plane of the eye and the vertical distance between the vertex of the anterior corneal surface and the equatorial plane of the eye.

4. The method for constructing a three-dimensional eyeball model according to claim 3, characterized in that: The establishment of parameters and variability analysis of the posterior half of the eyeball specifically include: Based on the wide-angle posterior segment OCT technology, the parameters of the posterior half of the eyeball are measured with the posterior part of the eyeball equatorial plane as the reference, and the parameters of the posterior half of the eyeball include the vertical distance O'M from the vertex of the posterior scleral macula to the equatorial plane of the eyeball; The variability analysis of the posterior half of the eye was performed based on the vertical distance between the central vertex of the posterior scleral macula and the ocular equatorial plane.

5. The method for constructing a three-dimensional eyeball model according to claim 4, characterized in that: The method of constructing the three-dimensional eyeball model by using corneal parameters, anterior half of the eyeball parameters and posterior half of the eyeball parameters specifically includes: S21-Acquire the corneal curvature R and the anterior scleral curvature R' based on IOLMaster; S22-constructing a corneal model OAB based on the corneal curvature R and the corneal diameter AB, wherein the corneal model OAB includes point O, point A, point B and a plurality of connecting lines; wherein point O is the vertex of the anterior surface of the cornea, point A and point B are points on the corneal margin corresponding to the corneal diameter, and point A and point B are located on both sides of point O respectively; S23-constructing the anterior half eyeball model OACO'DB based on the anterior half scleral curvature R', the eyeball transverse diameter CD passing through the eyeball equatorial plane, the vertical distance OO' between the vertex of the anterior surface of the cornea and the eyeball equatorial plane, and the corneal model OAB, wherein the anterior half eyeball model OACDB includes point O, point A, point B, point C, point O', point D, and a number of connecting lines, wherein point O' is the intersection of the vertical line passing through point O on the eyeball equator and the eyeball equator, point C and point D are two points on the eyeball equator corresponding to the eyeball transverse diameter passing through the eyeball equatorial plane, and point C and point D are located on both sides of point O respectively; S24-Acquire the axial length OM of the eyeball based on the IOLMaster, and determine the position of the posterior scleral macula center vertex M based on the axial length OM and the extension line of the line connecting the points O and O', wherein the posterior scleral macula center vertex M is located on the extension line of the line connecting the points O and O'; S25: Based on the position of the central vertex M of the posterior scleral macula and the model of the front half of the eyeball OACO'DB, a three-dimensional model of the eyeball is constructed, and the area formed by points O, A, C, D and B in the three-dimensional model of the eyeball is defined as a constant area with small variability, and the area formed by point C, the central vertex M of the posterior scleral macula and point D in the three-dimensional model of the eyeball is defined as a variable area with large variability.

6. A macular buckling surgery navigation system, characterized in that: It includes a model building module and a cingulum suture point calculation module; The model building module is configured as follows: accurately calculating the axial length of the eye through IOLMaster, determining the location of the fovea, evaluating the amount of macular splitting based on OCT, and estimating the amount of surgery; The cingulum suture point calculation module is configured to calculate the positions of the cingulum suture points P1 and P2 based on the three-dimensional model of the eyeball.

7. The macular buckling surgery navigation system according to claim 6, characterized in that: The buckle suture points P1 and P2 are respectively located beside the superior rectus muscle and the lateral rectus muscle in the superior temporal quadrant, and are located in the constant area; wherein, the buckle suture points P1 and P2 are determined based on the planned shortened axial length MM' and the distance between the buckle top pressure center and the terminal fixing ring, wherein the axial length MM' is the distance between the position of the fovea centralis and the shortened target fovea centralis M', and the target fovea centralis M' is located on the extension line of the vertical line between the apex of the anterior surface of the cornea and the equatorial plane of the eyeball.

Images