CN109581690B - Lenses, spectacles and methods for obtaining parameters of defocusing amount, fitting of glasses and evaluating effects - Google Patents

Abstract

The peripheral defocused lens comprises a central optical area, an annular defocused area is arranged outside the central optical area, and the defocused amount of the defocused area changes in the annular direction. At least one of the base arc zone and the reversal arc zone of the orthokeratology lens provided by the application has structural change in the circumferential direction. The method for acquiring the defocus quantity parameter comprises the following steps: collecting defocus amounts of a plurality of sampling points on a user cornea or a dioptric system consisting of a cornea and a lens of a myope, wherein the sampling points are distributed on a plurality of direction angles in a coordinate system taking the center of the cornea as an origin; and obtaining the defocus parameter according to the defocus of the plurality of sample points on the cornea. The application also provides a method for determining the myopia control effect of the orthokeratology lens on the myope according to the defocus quantity parameter.

Description

Lenses, spectacles and methods for obtaining parameters of defocus amount, fitting of glasses and evaluating effects

technical field

The present application relates to the field of myopia prevention and control, and more particularly, to a lens, glasses, a method for obtaining a defocus amount parameter, a method for fitting glasses and a method for evaluating the effect of myopia control.

Background technique

Myopia has become a major public health problem, and myopia has also become a major burden to society. The degree of deflection of light at the interface can be expressed by refractive power. The refractive power depends on the refractive indices of the two media and the radius of curvature of the interface. Myopia is a type of refractive error. For a normal eye, both central and peripheral images are projected on the retina. Due to the elongation of the eyeball in myopic eyes, in the relaxed state of accommodation, the focus of parallel light rays falls in front of the retina after being refracted by the refractive system of the eye.

The development mechanism of myopia is still under intense discussion, and studies have found many means to control the growth of the eye axis, including different concentrations of drugs and different optical design lenses. Peripheral defocus theory is one of the causes of myopia proposed by Professor Smith from the School of Optometry of the University of Houston at the end of the last century. According to the concept of refractive optics, when the focus falls in front of the retina, it is called myopic defocus, and when it falls behind the retina, it is called hyperopic defocus. Peripheral defocus theory believes that this hyperopic defocusing around the retina is the main reason for the continuous increase in the degree of myopia. The myopic defocusing around the retina can slow down the growth of the eye axis and has the effect of inhibiting the development of myopia.

The main purpose of traditional single vision glasses is to solve the wearer's need to see far away, and can only correct the defocus in the central macular area of the eye. Figure 1 is a schematic view of an eye corrected by a single vision lens. The image of the object at the central vision is projected on the retina, but the image of the object in the peripheral area is projected to the back of the retina, forming a hyperopic defocus. The eyeball adjusts so that the image of the peripheral area is projected onto the retina, which causes the axial length of the eye to slowly elongate. Therefore, after some patients wear ordinary myopia glasses, although the problem of blurred vision has been solved, the degree of myopia is still deepening.

The new peripheral defocus lens can reduce the hyperopic defocusing around the retina, and even make it myopic defocusing, in order to alleviate the growth of the eye axis. The specially designed optical lenses can be orthokeratology lenses (such as OK lenses (OrthoKeratology)), contact lenses (including soft contact lenses, hardware contact lenses such as RGP lenses, etc.) or frame glasses (such as prism bifocals) Lenses for spectacles, bifocal spectacles, progressive multifocal spectacles, etc.). After the myopia is corrected by the peripheral defocused lens, the image of the object at the central vision is projected onto the retina, and the image of the peripheral object is projected onto the retina or projected to the front of the retina, forming a myopic defocus effect, as shown in Figure 2. Some studies have found that the success rate of contact lenses with peripheral defocus in controlling myopia (ie, inhibiting the growth rate of the eye axis) can reach about 30% to 40%.

Orthokeratology lens adopts inverse geometric design to correct vision and control the development of myopia by changing the shape of the cornea. The success rate of controlling the development of myopia can reach 32%-55%. Unlike spectacles and contact lenses, orthokeratology lenses only need to be worn at night and do not need to be worn during the day to achieve normal vision. The design of orthokeratology lens is divided into VCT (vision shaping treatment) design and CRT (corneal refractive therapy) design. Among them, the orthokeratology lens designed by VST includes the base arc area, the reverse arc area, the positioning arc area and the peripheral arc area.

The middle of the lenses of contact lenses and frame glasses is usually a central optical zone with constant refractive power. For the peripheral defocus lens used for myopia control in this application, the refractive power of the peripheral area outside the central optical zone is higher than that of the central optical zone. area, the difference between the two refractive powers is expressed by the defocus amount, in D (degrees) as the unit. For example, if the power of the central optical zone of a lens for myopia is -2.00D (usually the power is used as the power of the lens), and the peripheral position has a defocusing amount of 4.5D, the power of the peripheral position of the lens is 2.5D. If the power of the central optical zone of the lens used for myopia is -5.00D, and the defocusing amount of the peripheral position is still 4.5D, the power of the peripheral position of the lens is -0.50D.

The design of the defocus amount of the peripheral defocus lens is related to the effect of myopia control, but which defocus amount parameters are related to myopia control (referring to controlling the development of myopia), and the mechanism of the association between the defocus amount parameters and myopia control is still unclear. Therefore, it is difficult to design and match the peripheral defocus lens in a targeted manner, which affects the myopia control effect that the peripheral defocus lens can achieve.

For orthokeratology lenses, the amount of defocus formed on the cornea is currently only an estimate of the total amount. No other defocus parameters related to myopia control were proposed. Moreover, the clinical prediction of the effect of orthokeratology still lacks standards, and it will take a long time to judge its myopia control effect on specific myopic patients. This has affected the application of orthokeratology lenses.

SUMMARY OF THE INVENTION

The following is an overview of the topics detailed in this article. This summary is not intended to limit the scope of protection of the claims.

An embodiment of the present invention provides a peripheral defocus lens, the lens includes a central optical zone, an annular defocus zone is provided outside the central optical zone, and the defocus amount of the defocus zone varies in the annular direction .

An embodiment of the present invention provides a frame glasses, comprising a frame and two lenses, characterized in that, at least one of the two lenses adopts the above-mentioned peripherally defocused lens.

An embodiment of the present invention provides a lens for an orthokeratology lens, the lens includes a base arc area, a reverse arc area and a positioning arc area, and at least one of the base arc area and the reverse arc area is in the circumferential direction There are structural changes.

An embodiment of the present invention provides a method for obtaining a defocus amount parameter, including: in a user's naked eye state, collecting defocus amounts of multiple sample points on the user's cornea, the sample points are distributed with the cornea center as the origin and, according to the defocus amounts of the plurality of sample points on the cornea, the defocus amount parameters are obtained.

An embodiment of the present invention provides a method for obtaining a defocus amount parameter, which includes: when a myopic patient wears a corneal contact lens, collecting defocus amounts of multiple samples on a refractive system composed of the cornea and the lens of the myopic patient , the sample points are distributed on a plurality of direction angles in a coordinate system with the cornea center as the origin; and, the defocus amount parameter is obtained according to the defocus amounts of the plurality of sample points on the refractive system.

An embodiment of the present invention provides a method for fitting glasses, comprising: obtaining a parameter of the amount of defocus in the naked eye state of a myopic patient before fitting glasses according to the method for obtaining a parameter of defocusing as described above; and, according to the amount of defocusing The parameters are glasses for the myopic patient.

The embodiment of the present invention provides a method for evaluating the control effect of myopia, including: obtaining the defocus amount parameter obtained in the naked eye state of the myopic patient after the orthokeratology lens is used for orthokeratology according to the above method; and, according to the method described above. The defocus amount parameter determines the myopia control effect of the orthokeratology lens on the myopic patient.

Other aspects will become apparent upon reading and understanding of the drawings and detailed description.

Description of drawings

Fig. 1 is a schematic diagram of hyperopic defocus generated when using single vision lens to correct myopia;

Fig. 2 is the schematic diagram of myopic defocus generated when using peripheral defocus lens;

Fig. 3A is a schematic diagram of the change of the defocus amount of the patient's cornea at the same direction angle with distance;

Figure 3B is a schematic diagram of the change of mRCRP in the patient's cornea in the range of 0 to 360 degrees;

Fig. 4 is the schematic diagram of each component in the established mRCRP model;

5 is a schematic diagram of the relationship between the maximum defocus amount Vmax and the length of the eye axis;

Fig. 6 is the schematic diagram that the success rate of myopia control changes with the change of Vmax;

7A-7D are schematic diagrams of several different situations of the values of each component in the mRCRP model;

8A and 8B are schematic diagrams of peripheral defocus lenses of two exemplary embodiments of the present invention;

9 is a schematic diagram of an orthokeratology lens according to an exemplary embodiment of the present invention;

Fig. 10 is the A-A sectional view of Fig. 9;

11 is a flowchart of a method for obtaining a defocus amount parameter according to an exemplary embodiment of the present invention;

12 is a flowchart of another method for obtaining a defocus amount parameter according to an exemplary embodiment of the present invention;

13 is a flowchart of a method for providing glasses according to an exemplary embodiment of the present invention;

14 is a flow chart of a method for evaluating the effect of myopia control provided by an exemplary embodiment of the present invention;

15 is a schematic diagram of a computer device of an exemplary embodiment of the present invention.

Detailed ways

This application describes a number of embodiments, but the description is exemplary rather than restrictive, and it will be apparent to those of ordinary skill in the art that within the scope of the embodiments described in this application can be There are many more examples and implementations. Although many possible combinations of features are shown in the drawings and discussed in the detailed description, many other combinations of the disclosed features are possible. Unless expressly limited, any feature or element of any embodiment may be used in combination with, or may be substituted for, any other feature or element of any other embodiment.

This application includes and contemplates combinations with features and elements known to those of ordinary skill in the art. The embodiments, features and elements that have been disclosed in this application can also be combined with any conventional features or elements to form unique inventive solutions as defined by the claims. Any features or elements of any embodiment may also be combined with features or elements from other inventive arrangements to form another unique inventive arrangement defined by the claims. Accordingly, it should be understood that any of the features shown and/or discussed in this application may be implemented alone or in any suitable combination. Accordingly, the embodiments are not to be limited except in accordance with the appended claims and their equivalents. Furthermore, various modifications and changes may be made within the scope of the appended claims.

Furthermore, in describing representative embodiments, the specification may have presented methods and/or processes as a particular sequence of steps. However, to the extent that the method or process does not depend on the specific order of steps described herein, the method or process should not be limited to the specific order of steps described. Other sequences of steps are possible, as will be understood by those of ordinary skill in the art. Therefore, the specific order of steps set forth in the specification should not be construed as limitations on the claims. Furthermore, the claims directed to the method and/or process should not be limited to performing their steps in the order written, as those skilled in the art will readily appreciate that these orders may be varied and still remain within the spirit and scope of the embodiments of the present application Inside.

In the present application, both the orthokeratology lens and the contact lens can be lenses made of gas permeable hard material (RGP, Rigid Gas Permeable), but they belong to two different types of glasses. Orthokeratology lenses are lenses designed with inverse geometry, the inner surface of which consists of multiple arc segments. The corneal geometry is changed through hydrodynamic effects, and it is worn on the front of the cornea when sleeping, gradually flattening the curvature of the cornea and shortening the axial length of the eye, so there is no need to wear it during the day. Contact lenses can also be called contact lenses. The lenses do not use inverse geometric design. They correct vision or protect the eyes through the optical effects produced by wearing on the cornea of the eye. According to the hardness of the material, it can include rigid , semi-hard, soft three. The lenses of frame glasses are mounted on the frame, and there is a distance between the lenses and the eyeballs.

One of the criteria for successful fitting of orthokeratology lenses is the creation of a centered central positioning, ie, the creation of a uniform peripheral defocus on the cornea. Studies have shown that the greater the refractive error of myopia, the greater the amount of peripheral defocus formed, and the control effect of myopia is relatively good. However, it is not mentioned which parameter is used to evaluate the defocus amount, and the size of the peripheral defocus amount will also be subject to various restrictions, so it cannot be made particularly large. The data range of the peripheral defocusing selected in the research of this conclusion is -1.00 ~ -6.00D. At the same time, there are also research conclusions to the contrary, that the amount of peripheral defocus is not necessarily related to the control effect of myopia. According to this research, the range of peripheral defocus data is generally selected. In addition, for contact lenses and spectacles, if a lens with excessive peripheral defocus is used, the patient will feel uncomfortable, resulting in decreased visual acuity and contrast sensitivity, and there are problems such as difficulty in manufacturing. At present, the peripheral defocusing design scheme adopted by the lenses of contact lenses and spectacles has a lower myopia control effect than orthokeratology lenses.

If the mechanism of orthokeratology lenses to relieve axial growth can be better explained, it will have great guiding significance for the clinical fitting of orthokeratology lenses, and the mechanism can be extended to the peripheral defocusing design of contact lenses and spectacle lenses. middle. Therefore, the inventors of the present application conducted a prospective study to explore the influence of factors such as corneal defocus shape and degree on the axial growth of myopic patients after wearing orthokeratology lenses.

For the amount of defocus, there are currently only estimates of the total amount or the assumption that a uniform peripheral defocus situation is formed after shaping. However, the inventors of the present application have found through research that different meridians of the retina have different responses to defocus due to corneal astigmatism and asphericity of the retina, and the peripheral defocus formed on the cornea after the patient wears an orthopedic lens is not uniform. It is unscientific to measure the influence of peripheral defocusing on myopia control by calculating the total or average value of peripheral defocusing. For patients with myopia of -1.00~-5.00D, which often occurs in clinical practice, the total amount of peripheral defocusing after orthokeratology is not much different, but the difference in the distribution of peripheral defocusing on the cornea after orthokeratology will cause defocusing on the cornea. The maximum value of the focal amount (the maximum value is also referred to as the extreme value in this application, and the position on the cornea with the maximum defocus amount can be one point or multiple points, which can be distributed together or discretely distributed in multiple places) . The retina is more sensitive to the defocus amount than the total amount, but the extreme value of the defocus amount, that is, it has extreme sensitivity. In the influence of peripheral defocusing on myopia control, the maximum defocusing amount on the cornea is more important than the total defocusing amount.

The inventor of the present application has carried out an experimental study on the relationship between the amount of defocus on the cornea and the control effect of myopia after children wear orthokeratology lenses. The experimental method is as follows:

Fifty-five adolescents aged 8-12 were enrolled as patients. All patients had no history of using myopia control products, no ocular surface diseases, and no systemic diseases affecting the refractive system. The patient's mydriatic refraction satisfied -5.50D≤SE≤-1.00D (SE is equivalent spherical lens diopter), corneal astigmatism ≤-1.50D, anisometropia less than 1.0D, and best corrected visual acuity higher than 20/20. After a comprehensive examination, the patients wore orthokeratology lenses (Euclid System Crop., Herndon, VA) produced by Euclid Company, USA. Corneal biomechanics was measured with an optical correlation biometer (Lenstar LS900, Haag-Streit AG, Switzerland). Corneal topography was checked using a corneal topograph (Oculus, Wetzlar, Germany) before wearing and four months after wearing. The data of the right eye of each patient were taken for statistics, and the normality of all data was tested by the Shapiro-Wilk test. The Ranksum test was used to compare the differences between the ideal and non-ideal myopia control groups in the model. Logistic regression analysis method was used to analyze the relationship between the success rate of myopia control and the maximum defocus amount.

In this experiment, the following method was used to accurately analyze the data obtained by corneal topography to determine the defocus parameter on the cornea: use Matlab software to determine the positioning of the lens. Taking the center of the cornea as the center, the cornea is divided into 36 fan-shaped areas, the central angle of each area is 10°, and multiple sample points are taken in each area, including one sample point at the center of the cornea to calculate other sample points defocus amount. These sample points can be evenly distributed in this area, or can be distributed on 36 directional angles spaced 10° in turn. The more sample points, the higher the calculation accuracy. For each region, the defocus amount of all samples in the region can be calculated from the corneal topography, as shown in Figure 3A. The horizontal axis in the graph represents the distance (ie, radial distance) of the point on the region from the center of the cornea. The vertical axis represents the refractive power of the point on the area. The refractive power of the center of the cornea in the figure is 40 degrees, and the refractive power of other points minus 40 is the defocus amount of that point. Take the largest defocus amount in the figure to represent the defocus amount in this area, denoted as mRCRP. mRCRP usually occurs in the corneal region corresponding to the inversion arc of orthokeratology lenses.

For each patient, 36 mPCRPs on 36 regions and their corresponding angles can be obtained. For example, the angle corresponding to the region from 0 to 10° can be set to 0° (or another value from 0° to 10°). , the angle corresponding to the area of 10°～20° can be set to 10° (or another value in 10°～20°), and so on. Perform curve fitting according to the 36 mPCRPs (that is, select an appropriate curve type to fit the observed data, and use the fitted curve equation to analyze the relationship between the two variables), and a defocus amount curve, called the mPCRP curve, can be obtained, such as shown in Figure 3B. The horizontal axis in FIG. 3B is the direction angle, the vertical axis is the mPCRP value, the circle in the figure is the position of the 36 mPCRPs in the figure, and the curve is the mRCRP curve. The maximum peak value of the defocus amount curve is recorded as Vmax, and Vmax is the maximum defocus amount on the cornea after shaping, which can also be referred to as the maximum defocus amount on the cornea.

For each patient, a model for accurately calculating mPCRP can be established based on the fitted defocus amount curve: mRCRP=M+F1+F2. Specifically, a multiple linear regression detection model can be used, and relevant factors include spherical equivalent lens, lens positioning, astigmatism and corneal eccentricity. R2=0.93±0.06 (mean 0.94). When performing linear regression analysis on variables in statistics, and using the least squares method for parameter estimation, R2 is the ratio of the regression sum of squares to the sum of squares of total deviations, indicating the proportion of the sum of squares of total deviations that can be explained by the sum of squares of regression , the larger the ratio, the more accurate the model and the more significant the regression effect.

Please refer to Figure 4. This model consists of three parts: M represents the average refractive power, which is related to the initial equivalent spherical lens before the patient wears orthokeratology lenses, and is represented as a horizontal dashed line in the figure; F1 is a sine The curve, which can be expressed as (Mean*f1*sin(x+phase1)), has a peak in the range of 360 degrees of direction angle, F1AmpF2 is the maximum value of F1; F2 is a cosine curve, which can be expressed as (Mean*f2* sin(2*x+phase2)), there are two peaks in the range of 360 degree direction angle, F2Amp is the maximum value of F2. Studies have shown that the magnitude of F1 amplitude f1 is related to the asymmetry of lens positioning (such as wearing bias, etc.). The peak f2 of F2 is related to corneal astigmatism. The values of the three specific parameters in the model can be calculated according to the defocus amount curve. The mRCRP curve obtained by the superposition of the three parts is represented by a solid line in the figure. The maximum value is Vmax and the minimum value is Vmin.

After wearing for one year, corneal biomechanics were measured for each patient, and 0.3 mm was used as the axial growth threshold for judging whether myopia control was effective. The results showed that among the 55 patients, 40 patients achieved effective myopia control, and the annual growth of the eye axis was less than or equal to 0.3mm. Combining the results of myopia control with the mRCRP curve of each patient, it can be found that the larger the Vmax of the patient's mRCRP curve, the higher the success rate. As shown in Figure 5, the horizontal axis represents the size of Vmax, and the vertical axis represents the length of the axial growth. Each circle corresponds to a patient, and the circle below the 0.3mm line corresponds to the patient whose myopia was successfully controlled. The 0.3mm line The circles above correspond to patients who have failed myopia control.

Figure 6 shows the relationship between Vmax and the success rate of myopia control, which shows that with the increase of Vmax, the success rate of myopia control increases (p<0.05). When Vmax≤1.2D, only 20% of patients succeeded; when Vmax≥3.5D, more than 50% of patients succeeded; when Vmax≥4.5D, more than 80% of patients succeeded; when Vmax≥5D, more than 90% of patients succeeded Patient success. According to this relationship, according to this statistical data, Vmax is used to evaluate, when Vmax≤1.2D, it can be considered that myopia control has a 20% probability of being effective; when Vmax≥3.5D, myopia control has a probability of more than 50% effective; Vmax ≥4.5D, the probability of myopia control is more than 80% effective; when Vmax≥5D, the probability of myopia control is more than 90% effective.

The above data are only exemplary, according to the analysis method proposed in this application or similar methods, more tests with a wider range (such as myopia children in different countries) can be carried out, and Vmax and the success rate of myopia control can be obtained statistically according to the data of these tests. The corresponding relationship and other specific data may not be exactly the same, which is a normal phenomenon.

Taking the threshold value as 4.5D as an example, the mRCRP curve established for each patient will be combined with myopia control to analyze whether it is successful. It can also be found that:

If the M value is large, although the mRCRP curve does not fluctuate, the defocus amount of each position on the cornea can reach 4.5D, as shown in Figure 7A, and myopia can still be effectively controlled at this time.

If the value of M is small and the fluctuation of the mRCRP curve is small, the defocus amount at no point on the cornea can reach 4.5D, as shown in Figure 7B, and there is no control effect at this time.

If the M value is in the mean value, but the mRCRP curve does not fluctuate much, and the defocus amount of no point on the cornea exceeds 4.5, as shown in Figure 7C, the control effect is not good at this time.

If M is small, but mRCRP fluctuates greatly, and the defocus amount of some points on the cornea exceeds 4.5D, as shown in Figure 7D, the control effect is better at this time.

In the model mRCRP=M+F1+F2 established for patients, the M value is related to the degree of myopia. For low to moderate myopia, the M value will be lower. According to the model, the increase of F1 and F2 will increase the Vmax and improve the control effect of myopia. Therefore, regarding the influence of peripheral defocusing on myopia control, the applicant proposes a new theory: the retina is sensitive to the extreme value of peripheral defocusing, and it is not necessary to have the same defocusing amount at all positions, as long as the maximum defocusing amount Vmax is large enough, it can be effective Control myopia. The greater the Vmax, the higher the success rate of myopia control. By comparing the patient's Vmax with the set defocus threshold (such as 3.5D, 4.5D), the effect of myopia control can be effectively evaluated. In addition, studies have shown that as long as one point of the shaped cornea reaches the defocus threshold, the success rate of myopia control can be evaluated according to the defocus threshold. Under the condition that the defocusing threshold is unchanged, if the area on the cornea where the defocusing amount reaches the defocusing threshold (which can be represented by the corresponding central angle) is larger, the success rate will also increase accordingly.

Although the above research is based on the orthokeratology lens as the source, the established model, and the proposed fluctuations and thresholds of peripheral defocus are suitable for the design of peripheral defocus lenses. The above theory provides important inspiration for lens design: under the condition that the total amount of defocusing remains unchanged, the uneven design of peripheral defocusing can increase Vmax, which is more beneficial to myopia control. This has a very important guiding significance for the lens design of both frame glasses and contact lenses.

In addition, the above analysis shows that in the model mRCRP=M+F1+F2 established for patients, the amplitudes of F1 and F2 are also related to the effect of myopia control. If one or both of F1 and F2 are larger, the success rate of myopia control is higher. high. It is easy to understand that if the amplitudes of F1 and F2 are large, the maximum peak value Vmax of mRCRP is generally larger. According to Figure 4, it can be seen that under the condition that the amplitudes of F1 and F2 remain unchanged, if one of the peaks of F1 and one of the two peaks of F2 are in the same direction angle, the two can be superimposed, then the obtained Vmax Maximum, myopia control is the best. On the contrary, the obtained Vmax will become smaller, and the control effect of myopia will also decrease. As mentioned earlier, F1 is related to the lens worn, and F2 is related to corneal astigmatism, so this gives another important inspiration for lens design and wearing: the maximum defocus amount brought by the lens and the maximum on the cornea. Aligning the defocus amount can realize the superposition of extreme values, which will help to improve the control effect of myopia.

To this end, exemplary embodiments of the present invention provide a peripheral defocus lens, which may but need not be circular. As shown in FIG. 8A , the lens 1 includes a central optical zone 11 , an annular defocus zone 12 is disposed outside the central optical zone, and the defocus amount of the defocus zone varies in the annular direction. In principle, a large amount of defocus is more beneficial to control the development of myopia, but if the amount of defocus is too large, it will cause discomfort for myopic patients, such as dizziness and other reactions, as well as limited visual field, decreased visual acuity and contrast sensitivity vision. adverse effects such as decline. Through the change of the defocus amount in the annular direction, under the condition that the maximum defocus amount remains unchanged, the defocus amount of a part of the defocus area can be reduced, so as to ensure the control effect of myopia and reduce these adverse effects.

In the exemplary embodiment shown in FIG. 8A , the central optical zone 11 of the lens 1 is a circular fixed focal zone, and the lens 1 includes a center of the lens (the “O” point in the figure) as the center of the circle. Circular defocused area. However, the present application is not limited to this, and the lens may also include a plurality of annular defocus areas with the center of the lens as the center of the circle. As shown in FIG. 8B , the lens 1 includes two annular defocus areas 12a and 12b, As an example, the two defocus areas 12a and 12b in the figure are spaced apart, and the middle may also be a fixed focus area with a defocus amount of 0. As shown in FIG. In other embodiments, more defocus regions may be provided. In the presence of multiple defocus regions, only part of the defocus regions may vary in the annular direction, that is, as long as there is a variation in the annular direction of one defocus region, it falls within the scope of coverage of the present application.

The shape of the defocusing zone in the present application is not necessarily a circular ring, but can also be an elliptical ring or other non-standard annular structures. The position of a point in the out-of-focus zone can be represented by the azimuth angle and radial distance of the point on a coordinate system with the center of the lens as the center of the circle. Radial distance refers to the distance from the point to the center of the lens. In FIG. 8A , it is defined that the orientation angle of 0° points to the right, and the orientation angle of point P in FIG. 8A is denoted as α. The defocus amount of the defocus area varies in the ring direction, that is, the defocus amount of the defocus area varies within a 360-degree direction angle range, in other words, when the direction angle changes from 0 to 360°, the defocus area There is a change in the amount of defocus at this direction angle in . The change can be gradual, with one or two or more peaks present over 360°. There may also be sudden changes such as stepped transitions, which are not limited in this application. At one direction angle of the same defocus area, the defocus amount of points with different radial distances may also fluctuate. In this case, the maximum value of the defocus amount on the direction angle can be used to represent the defocus area at the direction angle. defocus amount on .

From the radial point of view of the lens, when there is a defocus zone, the defocus amount can have a rise and a fall with the increase of the radial distance. When there are multiple defocused areas, there can be multiple rising and falling processes. The defocus amount of the area outside the defocus area may be smaller than the defocus area or equal to 0, and may also be equal to or greater than the defocus area, for example, the defocus amount increases with the radial distance. It can remain unchanged or continue to increase after the last defocus zone rises.

In the exemplary embodiment shown in FIG. 8A , the lens includes an indicator mark 13 for indicating the direction angle at the position where the defocus amount is the largest in the out-of-focus zone. The position with the largest defocus amount can be a point or an area including multiple points. If there are multiple positions with the largest defocus amount, a position can be selected to indicate, or each position can be indicated by an indicator 13 respectively. . The indicator can be integrally formed with the lens, or attached to the lens, or embedded in the lens. For example, the indicator can be a protrusion or a groove on the lens, or a marker attached to the corresponding position of the lens, or a marker in the lens or even a bubble. Although in the example in FIG. 8A , the indicator mark 13 is an upward arrow, the shape of the indicator mark may also be a bar, a dot, or any other symbols and the like. The indicator mark can directly indicate the position with the largest defocus amount in the defocused area. The arrow in the figure is used to indicate that the position with the largest defocus amount in the defocused area appears on the 90° direction angle. When the position with the largest defocus amount in the defocus area is an area, the direction angle of the center position of the area can generally be indicated, but deviations are allowed, which does not affect the use. The indicator can also indicate the position of the largest defocus amount in an indirect way, such as pointing in the opposite direction, and so on. After there is an indicator mark on the lens, it is convenient for myopic patients to align the position with the largest defocus amount on the cornea according to the indicator mark when wearing a contact lens (especially when wearing a contact lens). Accurate, realize the extreme value superposition of the defocus amount on the lens and the cornea, so that the maximum defocus amount of the refractive system formed by the two is as large as possible, so as to improve the effect of myopia control. The defocus amount on the cornea is mainly caused by corneal astigmatism, and the position with the largest defocus amount generally occurs near the 90° direction angle and the 270° direction angle. Its exact location can be determined by inspection.

In an exemplary embodiment of the present invention, the difference between the maximum value and the minimum value of the defocus amount in the defocus area is not less than 1D or 2D or 3D or 4D or 5D. This difference reflects the amplitude of the fluctuation of the defocus amount in the defocus area, and can be selected according to factors such as the defocus threshold, the power of the lens, and the patient's tolerance.

In an exemplary embodiment of the present invention, the lens is a contact lens, and the defocus area is located in an annular area with the center of the lens as the center of the circle, with an inner diameter of 3 mm to 4 mm and an outer diameter of 5 to 8 mm. In another exemplary embodiment of the present invention, the lens is a lens of frame glasses, and the defocus area is located in an annular area with the center of the lens as the center, an inner diameter of 6 mm to 8 mm, and an outer diameter of 8 to 12 mm . For lenses, the defocus zone needs to exclude the central optical zone on the lens and areas that have little or no effect on myopia control, such as areas where the projected light cannot effectively enter the pupil. Some frame glasses have a large defocus amount at the edge of the lens, but the defocus amount in the above area is not large, and it does not have a good myopia control effect. Therefore, when designing and calculating the defocus amount of the defocus area of the lens, it is necessary to design and calculate according to the range of the defocus area set above, so as to achieve an effective myopia control effect. It should be noted that, in addition to the out-of-focus area, the above-mentioned annular area may also include a central optical area and an outer area of the de-focused area.

In an exemplary embodiment of the present invention, the lens is a contact lens lens, and the defocus zone includes a defocus amount at any position that is not less than 2D or 2.5D or 3D or 3.5D or 4D or 4.5D or 5D or 5.5 D's high focal area. In another exemplary embodiment of the present invention, the lens is a lens of frame glasses, and the defocus zone includes a defocus amount at any position that is not less than 2.5D or 3D or 3.5D or 4D or 4.5D or 5D or 5.5D Or the high focal area of 6D.

In this application, the high-focus area is the area used to achieve the desired myopia control effect in the de-focus area. A de-focus threshold can be set, and the defocus amount of any position in the de-focus area is not less than the de-focus threshold. Determined as a high focal area. In this application, a point is also regarded as a special area. The lens of frame glasses has a certain distance from the eyeball, and the defocus amount on the lens can play a smaller role than that of contact lenses. Therefore, when determining the high focal area, a higher threshold can be selected when other conditions are the same.

In an example, the defocus threshold used to determine the high focal area may be selected from a corresponding defocus threshold with a success rate of myopia control above 50%, such as the above-mentioned 3.5D, 4D, 4.5D and so on. After wearing glasses, the defocus amount of the lens and the defocus amount of the patient's cornea can be superimposed on the extreme value, so that the maximum defocus amount of the refractive system composed of the lens and the cornea is greater than the maximum defocus amount of the lens, so in the lens When designing, the defocus amount of the designed high focal area can also be less than 3.5D. The selection of the specific defocus threshold can be based on the expected success rate of myopia control, the patient's corneal astigmatism, the patient's fit of the lens, the patient's tolerance to high defocus, the size of the clear field of view, and the degree of myopia of the patient. and other factors to be considered comprehensively.

For the embodiment shown in FIG. 8A , the high focus area includes one ring segment 121 provided in the defocus area, but it can also have more than two ring segments. In addition, the shape of the high focal region can also be a point shape or other shapes. This application is not limited to this.

In an exemplary embodiment of the present invention, the high focal area falls within one or two or more than three fan-shaped areas, the fan-shaped areas take the center of the lens as the center, and the sum of the central angles is not greater than 30° or 60° ° or 90° or 120° or 150°. The two sides of the fan-shaped area into which the high focal area falls are the two connecting lines between the center of the lens and the two points with the largest and smallest direction angles in the high focal area. When there are multiple sector-shaped regions, the multiple sector-shaped regions may be evenly distributed in the defocus zone, such as being centrally symmetric about the center of the lens, or axisymmetric about the diameter of the central optical zone, but not limited thereto. The smaller the sum of the central angles of the fan-shaped areas that the high focal area falls into, the smaller the other areas on the lens with less defocus (also known as the low focal area) are larger, which is conducive to improving wearing comfort and expanding clarity. Field of view, reducing the impact of high defocus on vision.

In an exemplary embodiment of the present invention, the defocus area includes one or two or more high focal areas, and the sum of the central angles of the ring segment where the high focal areas are located relative to the center of the lens is not less than 5° or 15° ° or 30° or 45° or 60°. In the example shown in FIG. 8A , there is a high focal area in the lens 1, and the central angle of the ring segment where it is located relative to the center of the lens is θ. The larger the sum of the above-mentioned central angles, the larger the proportion of the high focal area in the field of view, which is conducive to the control of myopia, but will reduce the clear field of view. The central angle corresponding to the high focal area can be expressed as the angle between the two connecting lines from the two points with the largest and smallest direction angles in the high focal area to the center of the lens.

In the above-mentioned two exemplary embodiments, the maximum and minimum values of the central angle corresponding to the high focal area are limited by the addition and addition, and an appropriate value can be selected according to the patient's condition during the actual fitting of glasses.

In an exemplary embodiment of the present invention, the defocus zone includes one or any combination of the following structures formed on the outer surface of the lens:

A surface with a gradual defocus amount;

fixed focus area; and

Dotted bulges.

In one example, the out-of-focus area includes a curved surface with a gradual de-focus amount formed on the outer surface of the lens. In one example, the defocus area includes a plurality of fixed focus areas formed on the outer surface of the lens (with a constant defocus amount within the area), the defocus amounts of the multiple fixed focus areas are different, and the distance between the multiple fixed focus areas is different. There is a step-like transition. In one example, the out-of-focus area includes point-like protrusions formed in a partial area of the outer surface of the lens (eg, in a ring segment with a central angle of 90 degrees), and the point-like protrusions constitute the center of the out-of-focus area. high focal area.

The above structures can also be combined, for example, in one example, the defocusing area includes one or more fixed-focus areas formed on the outer surface of the lens, and the fixed-focus area may constitute a part of the high-focus area but is not limited to Here, other areas adopt a curved surface structure with gradual defocus amount. In one example, the defocus area includes a curved surface with gradual defocus amount formed on the outer surface of the lens, which includes one or more high focal areas, and at least one high focal area is further provided with one or more high focal areas. A point-like protrusion, through this composite structure, a larger Vmax value can be obtained in the high focal area. and many more. Partial astigmatism may be caused when the outer surface of the lens forms a curved surface with gradual defocus amount, but a certain degree of astigmatism is acceptable, which is beneficial to the control of myopia.

In an exemplary embodiment of the present invention, the defocus amount of the defocus area forms a peak at a direction angle of 0 to 360°, and the peak value is not less than 2D or 2.5D or 3D or 3.5D or 4D or 4.5D or 5D or 5.5D; in another exemplary embodiment of the present invention, the defocus amount of the defocus area forms two peaks separated from each other by 120° to 240° at a direction angle of 0 to 360°, wherein the first The peak is not less than 2D or 2.5D or 3D or 3.5D or 4D or 4.5D or 5D or 5.5D, the second peak is equal to the first peak, or is smaller than the first peak. The above case with only one peak is equivalent to designing a structure on the lens to generate F1 in the above model, and the case of having two peaks is equivalent to designing a structure on the lens to generate F2 in the above model, it is Apply the defocus changes originally produced by corneal astigmatism to the lens design. Because human corneal astigmatism mostly occurs in the range centered on the 90° direction angle and the 270° direction angle (plus or minus 45°), the design of the above two peaks and their interval angles is helpful to achieve The extreme value of the defocus amount of the lens and the cornea is superimposed, resulting in a larger Vmax value, expanding the range of the high focal area in the field of view, and achieving better myopia control effect.

The peripheral defocus lens of the above-mentioned embodiment of the present invention adopts a new structure design such as a structure in which the defocus amount changes in the circumferential direction and a structure that is conducive to the superposition of the extreme value of the lens and cornea defocus amount, which can achieve better myopia control. Effect.

In an exemplary embodiment of the present invention, there is also provided a framed spectacles, comprising a frame and two lenses, at least one of the two lenses adopts any of the above-mentioned peripherally defocused lenses. In one example, the out-of-focus zone in the lens includes a high-focus zone above or below the center of the lens. In another example, the defocus area in the lens includes two high focal areas, one of which is located above the center of the lens and the other is located below the center of the lens; wherein the high focal area refers to the defocused area The defocus amount in any position is not less than 2.5D or 3D or 3.5D or 4D or 4.5D or 5D or 5.5D or 6D area. In this application, if an upward vertical line passing through the center of the lens passes through the high focal zone, the high focal zone is considered to be located above the center of the lens, and if a downward vertical line passing through the center of the lens passes through the high focal zone, then This high focal zone is considered to be below the center of the lens. The high focal zone is set above and/or below the center of the lens, also because it is considered that human corneal astigmatism occurs in the range centered on the 90° azimuth and 270° azimuth (plus or minus 45°) in most cases. left and right), this setting helps to achieve the extreme superposition of the defocus amount of the lens and the cornea. For a small number of people, corneal astigmatism will appear at other angles, and the needs of these people can be met by manufacturing and selecting lenses with high focal areas designed at other angles.

The above is the design of the peripheral defocus lens, the application also applies the above theory to the design of the orthokeratology lens, thereby providing a lens 2 of the orthokeratology lens, as shown in FIG. 9 and FIG. The lens includes a base arc area (ie, the central optical area) 21, a reverse arc area 22, a positioning arc area 23 and a peripheral arc area 24, wherein at least one of the base arc area 21 and the reverse arc area 22 is in the There are structural changes in the circumferential direction. The circumferential change here means that there is a structural change in the angular range of 0 to 360 degrees with the center of the lens as the center of the circle. Orthokeratology does not directly correct vision itself, but indirectly corrects vision and inhibits the development of myopia through orthokeratology. The traditional design is based on deforming the cornea into the shape of the basal arc to achieve the purpose of defocusing. However, in this embodiment, through the special design of the base arc region or the reversed arc region, the shaped cornea has fluctuations in the circumferential direction, and the expected maximum defocus amount can be achieved.

In an exemplary embodiment of the present invention, the reversal arc region includes at least two ring segments, two of which are shown in the figure, wherein the height of one ring segment 221 is greater than that of the other ring segments 222 , as shown in FIG. 10 . 9 In the A-A section of the lens, the orthokeratology is fastened on the cornea 3, and the height of the first ring segment 221 in the reversal arc region is greater than the height of the other ring segments 222. Increasing the height of the arc segment can increase the space for corneal deformation at this position, which is beneficial to increase the defocus amount at the corresponding position on the cornea after shaping. In another exemplary embodiment of the present invention, the reversal arc region can also be set as a highly gradual aspheric shape in the circumferential direction, so that the position on the cornea corresponding to the inversion arc region is defocused after shaping. direction change, resulting in better control of myopia. In addition, the reversal arc area can also be widened. For example, under the condition of ensuring stable positioning, the width of the reversal arc area can be increased from the conventional 1mm to 2mm to 1.2mm to 2.2mm or more. The width of the reversal arc area is increased, which helps to increase the defocus amount corresponding to the corneal position of the reversal arc area. For the base arc area, under the condition that the vision correction meets the requirements, an asymmetric structural design can also be used to achieve the effect of changing the defocus amount of the cornea in the circumferential direction after shaping.

Because the relationship between the amount of defocus and myopia control is unclear, in previous practice, only the amount of defocus on the cornea was considered. According to the above-mentioned new theory of defocusing and myopia control proposed in this application, the embodiment of the present invention provides the following method for obtaining the defocusing amount parameter, so that the defocusing amount parameter associated with the myopia control can be obtained and used in occasions such as glasses matching .

As shown in FIG. 11 , an exemplary embodiment of the present invention provides a method for obtaining a defocus amount parameter, including:

Step 110, in the user's naked eye state, collect the defocus amounts of a plurality of sample points on the user's cornea, and the sample points are distributed on a plurality of direction angles in a coordinate system with the cornea center as the origin;

The acquisition of the defocus amount on the cornea can be realized using a corneal mapper, a new type of equipment that presents the curvature image of the corneal surface with the aid of a computer, and can generate a corneal topography map. According to the corneal topography, the defocus amount of the selected spot on the cornea can be calculated.

Step 120, obtaining a defocus amount parameter according to the defocus amounts of the multiple sample points on the cornea.

In an exemplary embodiment of the present invention, in the naked eye state of the user, it means that the defocus amount parameter obtained in the naked eye state before the myopia patient is fitted with glasses is used for fitting glasses for the myopic patient; In another exemplary embodiment of the present invention, in the naked eye state of the user, it refers to the defocus amount parameter obtained in the naked eye state of the myopic patient after corneal orthokeratology is performed by an orthokeratology lens. To evaluate the myopia control effect of the myopic patients after wearing orthokeratology lenses. The orthokeratology lens worn by the myopic patient in this embodiment may be the orthokeratology lens of the embodiment of the present invention, or may be other orthokeratology lenses such as traditional orthokeratology lenses.

In an exemplary embodiment of the present invention, the defocus amount parameter includes one or any combination of the following parameters:

the amount of defocus of a plurality of sample points on the cornea;

the maximum amount of defocus on the cornea;

position information on the cornea where the maximum defocus amount is located;

the comparison result of the maximum defocus amount on the cornea and the set one or more defocus thresholds;

One or more of the presence, quantity, size and location of the effective defocus area;

Wherein, the maximum defocus amount on the cornea is determined according to the defocus amounts of a plurality of sample points on the cornea, and the effective defocus area refers to the area where the defocus amount at any position on the cornea is not less than the corresponding defocus threshold. area, the defocus threshold is not less than 3.5D or 4D or 4.5D or 5D or 5.5D.

In an example, determining the maximum defocus amount on the cornea according to the defocus amounts of a plurality of sample points on the cornea, including:

The maximum defocus amount on the cornea is taken as the maximum defocus amount on the cornea. This method also has higher accuracy if there are enough samples. At this time, the position information of the maximum defocus amount on the cornea is the position information of the sample point with the maximum defocus amount; or

The maximum value of the defocus amount at each direction angle is determined according to the defocus amount of the sample point at each direction angle in the plurality of direction angles; according to the curve fitting of the defocus amount at each direction angle, 0° is obtained Defocus amount curve at a direction angle of ~360°; the maximum peak value of the defocus amount curve is determined as the maximum defocus amount on the cornea.

In addition to the above methods, in an example, multiple sample points on the cornea are evenly distributed on the peripheral membrane, and surface fitting can also be performed according to the multiple sample points, and the maximum peak value of the fitted surface can be used as the The maximum amount of defocus on the cornea. This application does not limit the specific calculation method.

There are different ways to select the sample points on the cornea. For example, the sample points may be selected at at least 18 equally spaced azimuth angles, and the defocus amount of at least 3 sample points may be collected on each azimuth angle. For another example, the defocus amount of at least 50 sample points can also be collected at 360 equally spaced directional angles, and at each directional angle. Specifically, it can be set according to actual needs such as measurement accuracy requirements.

An exemplary embodiment of the present invention also provides a method for obtaining a defocus amount parameter, as shown in FIG. 12 , including:

Step 210, when the myopic patient wears the corneal contact lens, collect the defocus amounts of multiple sample points on the refractive system composed of the cornea and the lens of the myopic patient, and the sample points are distributed in a coordinate system with the center of the cornea as the origin on multiple directional angles in;

The defocus amounts of the multiple sample points on the above-mentioned refractive system can also be detected by using a corneal map or similar detection equipment. The defocus amount of the plurality of sample points on the refractive system in this embodiment refers to the defocus amount of the plurality of sample points on the front surface of the refractive system.

Step 220: Obtain a defocus amount parameter according to the defocus amounts of multiple sample points on the refractive system.

The defocus amount parameter obtained in this step is the defocus amount parameter on the refractive system.

The corneal contact lenses in this embodiment may use the lenses with the peripheral defocus of the present application, or may not use the lenses with the peripheral defocus of the present application.

In an exemplary embodiment of the present invention, the obtained defocus amount parameter includes one or any combination of the following parameters:

the maximum amount of defocus on the refractive system;

The comparison result of the maximum defocus amount on the refractive system and the set one or more defocus thresholds;

Wherein, the maximum defocus amount on the refractive system is determined according to the defocus amounts of multiple sample points on the refractive system, and the defocus threshold is not less than 3.5D or 4D or 4.5D or 5D or 5.5D. For the method of determining the maximum defocus amount on the refractive system, reference may be made to the method for determining the maximum defocus amount on the cornea above, which will not be repeated here.

In one example, a defocusing threshold is set, such as a threshold for judging whether myopia control is successful, such as 4.5D, while in another example, multiple defocusing thresholds are set such as 3.5D and 4.5D or more. More than one, comparing the maximum defocus amount with a plurality of defocus thresholds can more accurately represent the interval where the maximum defocus amount is located, and quantitatively evaluate the effectiveness of myopia control.

In an exemplary embodiment of the present invention, the defocus amount parameter obtained according to the defocus amounts of multiple sample points on the refractive system includes: determining the effective defocus area according to the defocus amounts of the multiple sample points None, one or more information in quantity, size and position, wherein, the effective defocus area refers to the area where the defocus amount at any position on the refractive system is not less than the corresponding defocus threshold, and the defocus area The threshold is not less than 3.5D or 4D or 4.5D or 5D or 5.5D.

In this embodiment, according to different corresponding defocus thresholds, there may be one or more effective defocus areas, and different effective defocus areas are determined by using different defocus thresholds. For example, there may be an effective out-of-focus area corresponding to a defocus threshold of 3.5D, an effective out-of-focus area corresponding to a defocus threshold of 4.5D, and so on. The number of the same effective defocus area can be one or more. There is an effective defocus area, which means that the maximum defocus amount on the refractive system is greater than the defocus threshold corresponding to the effective defocus area. Combined with the size information of the effective defocus area, the effectiveness of myopia control can be more refined. Evaluate. The size information of the effective out-of-focus area can be represented by the size of the central angle corresponding to the effective out-of-focus area, or the area of the effective out-of-focus area. In addition to the size information, other information of the effective defocus area, such as specific position information, can also be combined with the correlation between these position information obtained by statistical analysis and the effectiveness of myopia control for fine evaluation.

In an exemplary embodiment of the present invention, the glasses worn by the myopic patient are contact lenses, the contact lenses use any of the lenses described in the embodiments of the present invention, and the lenses include an indicator mark, the The indication mark is used to indicate the position with the largest defocus amount in the defocus area of the lens; before collecting the defocus amounts of the multiple sample points on the refractive system, the method further includes: according to the indication of the lens mark, and calibrate the wearing angle of the lens, so that the position with the largest defocus amount in the defocus area of the lens is aligned with the position on the cornea of the myopic patient where the maximum defocus amount is located. Because myopia patients should perform calibration first to obtain a good myopia control effect, the above calibration should also be performed before measuring the defocus parameter, which is beneficial to obtain more accurate data. The calibration of the position can be realized by rotating the lens by an angle with the line connecting the center of the lens and the center of the cornea as the axis after the center of the lens is aligned with the center of the cornea.

After obtaining the above defocus amount parameter, the obtained defocus amount parameter is used to evaluate the myopia control effect of the myopic patient wearing the contact lens, for example, evaluating the patient wearing a traditional peripheral defocus contact lens For the effect of myopia control, if the effect is not good, other lenses can be replaced in time, such as the peripheral defocus lens of the present application.

In an exemplary embodiment of the present invention, the defocus amount parameter includes a maximum defocus amount on the cornea, or a comparison result between the maximum defocus amount on the cornea and a set defocus threshold; The determining the myopia control effect according to the defocus amount parameter includes: judging whether the maximum defocus amount on the cornea is not less than the defocus threshold according to the defocus amount parameter, and if so, determining that the myopia control effect is effective, If not, determine that the myopia control effect is ineffective; or

The defocus amount parameter includes a maximum defocus amount on the cornea, or a comparison result between the maximum defocus amount on the cornea and a plurality of set defocus thresholds; the defocus amount parameter is determined according to the defocus amount parameter. Myopia control effect, including: judging whether the maximum defocus amount on the cornea is not less than one or more defocus thresholds according to the defocus amount parameter, and if so, according to the largest one or more defocus thresholds The defocus threshold is used to find the corresponding myopia control success rate, and the myopia control effect is determined according to the myopia control success rate.

In an exemplary embodiment of the present invention, the defocus amount parameter includes at least information on the presence or absence of an effective defocus area and size; the determining the myopia control effect according to the defocus amount parameter includes: If there is an effective defocus area, the corresponding myopia control success rate is searched according to the defocus threshold corresponding to the effective defocus area and the size information of the effective defocus area, and the myopia control effect is determined according to the myopia control success rate.

In the above embodiment, determining the myopia control effect according to the myopia control success rate includes: directly using the myopia control success rate to represent the myopia control effect; or, judging whether the myopia control success rate is not less than an expected success rate. If yes, determine that the myopia control effect is valid, if not, determine that the myopia control effect is invalid.

An exemplary embodiment of the present invention also provides a method for dispensing glasses, as shown in FIG. 13 , including:

Step 310, according to any method described in the above-mentioned embodiments of the present invention, obtain the defocus amount parameter of the myopic patient under the naked eye state before the glasses are fitted;

Step 320, according to the defocus amount parameter, the myopia patient is fitted with glasses.

The above-mentioned glasses can be a pair of suitable glasses selected from the manufactured glasses, or a new personalized glasses designed for myopic patients. The glasses may use the peripheral defocus lens of the present application, or may use the conventional peripheral defocus lens.

In an exemplary embodiment of the present invention, the defocus amount parameter includes the maximum defocus amount on the cornea and its position information; according to the defocus amount parameter, fitting glasses for the myopic patient includes: The myopic patient selects a peripheral defocused contact lens or lenses of frame glasses, so that after the maximum defocus amount on the cornea of the myopia patient is aligned and superimposed with the defocus amount at the corresponding position of the lens, the obtained sum is not Less than the set defocus threshold, wherein, the defocus threshold is not less than 3.5D or 4D or 4.5D or 5D or 5.5D, and the defocus threshold can be selected according to the desired myopia suppression effect and the patient's tolerance. Set one. The lens of the contact lens is directly attached to the cornea, and the center of the lens needs to be aligned with the center of the cornea before alignment. For frame glasses, there is a certain distance between the lens and the cornea. Before alignment, the center of the lens can be aligned with the cornea. The corresponding relationship of other positions can refer to the original rules.

In an exemplary embodiment of the present invention, the defocus amount parameter includes defocus amount information of a plurality of sample points on the cornea; fitting glasses for the myopic patient according to the defocus amount parameter includes: Myopic patients can choose contact lenses or spectacle lenses with peripheral defocus, so that when the myopic patient wears the lenses, the defocus amount on the cornea and the defocus amount at the corresponding position of the lens are aligned and superimposed. After that, there is at least an effective defocus area and the size of the effective defocus area meets the requirements, wherein the effective defocus area refers to an area where the defocus amount at any position is not less than the corresponding defocus threshold, and the defocus threshold is not equal to If it is less than 3.5D or 4D or 4.5D or 5D or 5.5D, a defocus threshold can be selected according to the desired myopia suppression effect and the patient's tolerance.

In an example, the size of the effective defocus area meets the requirements, including: the effective defocus area satisfies one or more of the following conditions:

The central angle of the ring segment where the effective defocus area is located relative to the center of the lens is not less than an angle threshold, and the angle threshold is a set value not less than 5° or 15° or 30° or 45° or 60°;

The sum of the areas of the effective out-of-focus areas is not less than the set area threshold.

In an exemplary embodiment of the present invention, the lens adopts any lens described in the embodiment of the present invention; before performing the alignment and stacking, the method further includes: calibrating the wearing angle of the lens (may be Completed in the software), the position with the largest defocus amount in the defocus zone of the lens is aligned with the position where the maximum defocus amount is located on the cornea of the myopic patient. By aligning before stacking, more accurate defocus data can be obtained, reducing the value of the required maximum defocus amount.

In an exemplary embodiment of the present invention, the method further includes: acquiring the diameter of the pupil of the myopic patient; matching frame glasses or contact lenses for the myopic patient, wherein the diameter of the pupil is determined according to the diameter of the pupil. The diameter of the central optical zone of the lens, the larger the diameter of the pupil, the larger the diameter of the central optical zone of the lens is determined. Here is a personalized design based on the patient's pupil size. For example, the diameter of the pupil can be divided into 5 grades of different sizes, and the diameter of the central optical zone of the lens can also be divided into 5 grades of different sizes. If the diameter of the pupil is the smallest order, the lens with the diameter of the central optic zone is the smallest order, and if the diameter of the pupil is the largest order, the lens with the diameter of the central optic zone is the largest order. So on and so forth. In other examples, the number of pupil diameters graded and the lenses graded need not be equal. Moreover, the diameter of the pupil can also be divided into multiple sections without any grades, and each section corresponds to the diameter of the central optical zone of the lens, which is also possible.

At present, to judge whether an orthokeratology lens is effective in controlling myopia, it is necessary to measure the change of the eye axis after wearing the orthokeratology lens for one year, and the evaluation mainly focuses on the positioning and vision of the orthokeratology lens. This takes a lot of time and may delay the use of other modalities for effective treatment in patients with ineffective control.

To this end, an exemplary embodiment of the present invention provides a method for evaluating the control effect of myopia by using the defocus amount, as shown in FIG. 14 , including:

Step 410, according to any method described in the above-mentioned embodiments of the present invention, obtain the defocus amount parameter obtained in the naked eye state of the myopic patient after orthokeratology lens orthokeratology;

Step 420: Determine the myopia control effect of the orthokeratology lens on the myopia patient according to the defocus amount parameter.

In an exemplary embodiment of the present invention, the defocus amount parameter includes a maximum defocus amount on the cornea, or a comparison result between the maximum defocus amount on the cornea and a set defocus threshold; the Determining the myopia control effect according to the defocus amount parameter includes: judging whether the maximum defocus amount on the cornea is not less than the defocus threshold according to the defocus amount parameter, and if so, determining that the myopia control effect is effective, such as No, determine that the myopia control effect is invalid; or

The defocus amount parameter includes a maximum defocus amount on the cornea, or a comparison result between the maximum defocus amount on the cornea and a plurality of set defocus thresholds; the defocus amount parameter is determined according to the defocus amount parameter. Myopia control effect, including: judging whether the maximum defocus amount on the cornea is not less than one or more defocus thresholds according to the defocus amount parameter, and if so, according to the largest one or more defocus thresholds The defocus threshold is used to find the corresponding myopia control success rate, and the myopia control effect is determined according to the myopia control success rate. The success rate of myopia control corresponding to the defocus threshold can be obtained and saved according to the corresponding experimental data.

In an exemplary embodiment of the present invention, the defocus amount parameter includes at least information on the presence or absence of an effective defocus area and size information (when there is no effective defocus area, the size information and the like are empty information); Quantitative parameters to determine the myopia control effect, including: if there is an effective defocus area on the cornea, searching for the corresponding myopia control success rate according to the defocus threshold corresponding to the effective defocus area and the size information of the effective defocus area , and the myopia control effect is determined according to the myopia control success rate. The success rate of myopia control corresponding to the defocus threshold and the size information of the effective defocus area can be obtained and saved according to the corresponding experimental data. If the defocus amount parameter includes multiple effective defocus regions corresponding to different defocus thresholds, multiple myopia control success rates can be found, and one of them can be selected to determine the myopia control effect. For example, the myopia control success rate is searched according to the effective defocus area corresponding to the maximum defocus threshold and its size information, and the myopia control effect is determined using the found myopia control success rate, but the present application is not limited thereto. It is also possible to comprehensively consider the myopia control success rate found according to multiple effective defocus areas and their size information, such as taking a maximum value, an average value, or a minimum value to determine the myopia control effect, which is not limited in this application.

In the above exemplary embodiment of the present invention, the determining the myopia control effect according to the myopia control success rate includes: directly using the myopia control success rate to represent the myopia control effect; or, judging whether the myopia control success rate is It is not less than the expected success rate. If it is, it is determined that the myopia control effect is valid, if not, it is determined that the myopia control effect is invalid.

In an exemplary embodiment of the present invention, the evaluation of the myopia control effect is carried out within 2 weeks or within 1 month or within 3 months or within 6 months after the myopia patient wears the orthokeratology lens.

Different from the previous evaluation methods, the above-mentioned embodiment of the present invention provides a method for evaluating the effectiveness of myopia control by using the defocus amount parameter. Moreover, in a relatively short period of time, it is possible to predict whether the orthokeratology lens is effective for the patient, improve the clinical efficiency, and avoid delaying the patient's condition to choose other means of controlling myopia. This application provides a new evaluation standard for orthokeratology lenses, which is of great significance.

The method for obtaining the defocus amount parameter, the method for fitting glasses, and the method for evaluating the control effect of myopia in the above-mentioned embodiments of the present invention can all be implemented by using computer equipment. As shown in FIG. 15, the computer device includes a processor 50, a memory 60, and a computer program stored on the memory 60 and executable on the processor 50, when the processor 50 executes the computing program The processing of any of the methods described in the above embodiments of the present invention is implemented.

An exemplary embodiment of the present invention further provides a computer-readable storage medium on which a computer program is stored, and when the computer program is executed by a processor, implements the processing of any of the methods described in the foregoing embodiments of the present invention.

Those of ordinary skill in the art can understand that all or some of the steps in the methods disclosed above, functional modules/units in the systems, and devices can be implemented as software, firmware, hardware, and appropriate combinations thereof. In a hardware implementation, the division between functional modules/units mentioned in the above description does not necessarily correspond to the division of physical components; for example, one physical component may have multiple functions, or one function or step may be composed of several physical components Components execute cooperatively. Some or all physical components may be implemented as software executed by a processor, such as a central processing unit, digital signal processor or microprocessor, or as hardware, or as an integrated circuit, such as an application specific integrated circuit . Such software may be distributed on computer-readable media, which may include computer storage media (or non-transitory media) and communication media (or transitory media). As is known to those of ordinary skill in the art, the term computer storage media includes both volatile and nonvolatile implemented in any method or technology for storage of information such as computer readable instructions, data structures, program modules or other data flexible, removable and non-removable media. Computer storage media include, but are not limited to, RAM, ROM, EEPROM, flash memory or other memory technology, CD-ROM, digital versatile disk (DVD) or other optical disk storage, magnetic cartridges, magnetic tape, magnetic disk storage or other magnetic storage devices, or may Any other medium used to store desired information and which can be accessed by a computer. In addition, communication media typically embodies computer readable instructions, data structures, program modules, or other data in a modulated data signal such as a carrier wave or other transport mechanism, and can include any information delivery media, as is well known to those of ordinary skill in the art .

Claims (18)

1. A method of obtaining defocus parameters, comprising:

in a naked eye state of a user, acquiring defocus amounts of a plurality of sampling points on a cornea of the user, wherein the sampling points are distributed on a plurality of direction angles in a coordinate system taking the center of the cornea as an origin;

obtaining defocus parameters according to defocus of a plurality of sample points on the cornea, wherein the defocus parameters are used for fitting a lens for a myope or evaluating the myopia control effect of the myope after wearing a cornea shaping lens, and the defocus parameters comprise one or any combination of the following parameters:

a maximum defocus on the cornea;

position information of a maximum defocus on the cornea;

the maximum defocus amount on the cornea and one or more set defocus threshold values;

one or more of the presence, number, size and position of the effective defocus area;

the maximum defocus on the cornea is determined according to the defocus of the plurality of sample points on the cornea, the effective defocus area refers to an area where the defocus at any position on the cornea is not less than a corresponding defocus threshold, and the defocus threshold is not less than 3.5D, 4D, 4.5D, 5D, or 5.5D.

2. The method of claim 1, wherein:

determining the maximum defocus amount on the cornea according to the defocus amounts of a plurality of sample points on the cornea, wherein the method comprises the following steps:

taking the maximum value of the defocus amounts of the plurality of sample points on the cornea as the maximum defocus amount on the cornea; or

Determining the maximum value of the defocusing amount of each direction angle according to the defocusing amount of the sample point of each direction angle in the plurality of direction angles; performing curve fitting according to the defocusing amount on each direction angle to obtain a defocusing amount curve on the direction angle of 0-360 degrees; and determining the maximum peak value of the defocus curve as the maximum defocus on the cornea.

3. The method of claim 1 or 2, wherein:

in the naked eye state of the user, the defocusing amount parameter is obtained in the naked eye state before glasses fitting of a myope, and the obtained defocusing amount parameter is used for glasses fitting of the myope; or

In the naked eye state of the user, the defocusing amount parameter obtained in the naked eye state of a myope after the cornea of the myope is shaped by the corneal shaping lens is used for evaluating the myopia control effect of the myope after the myope wears the corneal shaping lens.

4. A method of obtaining defocus parameters, comprising:

when a myope wears a corneal contact lens, acquiring defocus amounts of a plurality of sampling points on a dioptric system consisting of the cornea and a lens of the myope, wherein the sampling points are distributed on a plurality of direction angles in a coordinate system taking the center of the cornea as an origin;

obtaining a defocus parameter according to defocus of a plurality of sample points on the dioptric system, wherein the defocus parameter is used for evaluating the myopia control effect of the myope wearing the corneal contact lens, and the defocus parameter comprises one or any combination of the following parameters:

a maximum defocus amount on the dioptric system;

the comparison result of the maximum defocus amount on the dioptric system and one or more set defocus thresholds;

determining the existence, the quantity, the size and the position of an effective defocusing area according to the defocusing amount of the plurality of sample points;

the maximum defocus amount on the dioptric system is determined according to defocus amounts of a plurality of sample points on the dioptric system, and the defocus threshold value is not less than 3.5D, 4D, 4.5D, 5D or 5.5D;

the effective defocus area refers to an area where the defocus amount at any position on the dioptric system is not less than the corresponding defocus threshold.

5. The method of claim 4, wherein:

the glasses worn by the myope are corneal contact lenses, the lenses of the corneal contact lenses comprise a central optical area, an annular defocus area is arranged outside the central optical area, defocus of the defocus area varies in the annular direction, and the lenses further comprise an indicating mark for indicating the position of the lens with the largest defocus in the defocus area;

before the defocus amounts of a plurality of sample points on the dioptric system are collected, the method further comprises the following steps: and calibrating the wearing angle of the lens according to the indication mark of the lens, so that the position with the maximum defocus amount in the out-of-focus area of the lens is aligned with the position with the maximum defocus amount on the cornea of the myope.

6. A method of fitting a lens, comprising:

acquiring a defocus parameter of a myope in an naked eye state before fitting according to the method of claim 1 or 2;

and fitting the glasses for the myope according to the defocus quantity parameter.

7. The method of claim 6, wherein:

the defocus parameter comprises the maximum defocus on the cornea and the position information of the maximum defocus;

fitting a pair of glasses for the myope according to the defocus quantity parameter, comprising: and selecting peripheral out-of-focus lenses of contact lenses or frame glasses for the myope, wherein the sum of the maximum out-of-focus on the cornea of the myope and the out-of-focus at the corresponding position of the lenses is not less than a set out-of-focus threshold value after overlay, wherein the out-of-focus threshold value is not less than 3.5D or 4D or 4.5D or 5D or 5.5D.

8. The method of claim 6, wherein:

the defocus parameter comprises defocus information of a plurality of sample points on the cornea;

fitting a pair of glasses for the myope according to the defocus quantity parameter, comprising: and selecting a peripheral out-of-focus lens of a contact lens or frame glasses for the myope, so that when the myope wears the lens, after the out-of-focus amount on the cornea is superposed with the out-of-focus amount at the corresponding position of the lens in an alignment manner, at least an effective out-of-focus area exists and the size of the effective out-of-focus area meets the requirement, wherein the effective out-of-focus area refers to an area with the out-of-focus amount at any position not less than a corresponding out-of-focus threshold value, and the out-of-focus threshold value is not less than 3.5D or 4D or 4.5D or 5.

9. The method of claim 8, wherein:

the size of the effective defocusing area meets the requirement, and the method comprises the following steps: the effective defocus area satisfies one or more of the following conditions:

the central angle of the ring section where the effective defocusing area is located relative to the center of the lens is not less than an angle threshold value, and the angle threshold value is a set value which is not less than 5 degrees, 15 degrees, 30 degrees, 45 degrees or 60 degrees;

the sum of the areas of the effective defocusing areas is not less than a set area threshold.

10. The method of claim 7 or 8, wherein:

the lens comprises a central optical area, an annular out-of-focus area is arranged outside the central optical area, the out-of-focus amount of the out-of-focus area changes in the annular direction, and the lens further comprises an indicating mark for indicating the position with the largest out-of-focus amount in the out-of-focus area of the lens;

before the performing the overlay, the method further includes: and calibrating the wearing angle of the lens, so that the position with the maximum defocus amount in the out-of-focus area of the lens is aligned with the position with the maximum defocus amount on the cornea of the myope.

11. The method of claim 6, wherein the method further comprises:

acquiring the diameter of the pupil of the myope;

and selecting a lens of a frame glasses or a corneal contact lens for the myope, wherein the diameter of the central optical area of the lens is determined according to the diameter of the pupil, and the larger the diameter of the pupil is, the larger the diameter of the determined central optical area of the lens is.

12. A computer device comprising a memory, a processor and a computer program stored on the memory and executable on the processor, characterized in that the processor implements the process of the method according to any one of claims 1 to 11 when executing the computer program.

13. A computer device for assessing the effects of myopia control, comprising a memory, a processor and a computer program stored on the memory and executable on the processor, wherein the processor when executing the computer program implements the processes of:

acquiring defocus parameters obtained by a myope in an naked eye state after the cornea of the myope is shaped by a keratoplasty mirror according to the method of claim 1 or 2;

and determining the myopia control effect of the corneal shaping mirror on the myope according to the defocus quantity parameter.

14. The computer device of claim 13, wherein:

the defocus parameter comprises the maximum defocus on the cornea or the comparison result of the maximum defocus on the cornea and a set defocus threshold; the method for determining the myopia control effect according to the defocus quantity parameter comprises the following steps: judging whether the maximum defocus amount on the cornea is not smaller than the defocus threshold value or not according to the defocus amount parameter, if so, determining that the myopia control effect is effective, and if not, determining that the myopia control effect is ineffective; or

The defocus parameter comprises the maximum defocus on the cornea or the comparison result of the maximum defocus on the cornea and a plurality of set defocus threshold values; the method for determining the myopia control effect according to the defocus quantity parameter comprises the following steps: and judging whether the maximum defocus amount on the cornea is not less than one or more defocus threshold values according to the defocus amount parameter, if so, searching for a corresponding myopia control success rate according to the maximum defocus threshold value in the one or more defocus threshold values, and determining a myopia control effect according to the myopia control success rate.

15. The computer device of claim 13, wherein:

the defocus amount parameters at least comprise the existence and size information of an effective defocus area;

the method for determining the myopia control effect according to the defocus quantity parameter comprises the following steps: if the cornea has the effective out-of-focus area, searching the corresponding myopia control success rate according to the out-of-focus threshold corresponding to the effective out-of-focus area and the size information of the effective out-of-focus area, and determining the myopia control effect according to the myopia control success rate.

16. The computer device of claim 14 or 15, wherein:

the determining of the myopia control effect according to the myopia control success rate comprises:

directly using the myopia control success rate to represent a myopia control effect; or

And judging whether the success rate of the myopia control is not less than the expected success rate, if so, determining that the myopia control effect is effective, and if not, determining that the myopia control effect is ineffective.

17. The computer device of any of claims 13 to 15, wherein:

the myopia control effect is assessed within 2 weeks or within 1 month or within 3 months or within 6 months of the myope wearing the keratoplastic lens.

18. A computer-readable storage medium, on which a computer program is stored, which, when being executed by a processor, carries out the processing of the method according to any one of claims 1 to 11.

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