Spectacle lens calculation taking account of the peripheral refraction

Abstract

The present invention relates to improving the individual adaptation of at least one spectacle lens for efficient control of the development of myopia and good tolerance of the spectacle lens. In this context, a method for determining individual prescription data for a spectacle wearer, which encompass peripheral refraction data for at least one eye of the spectacle wearer, is proposed, the method comprising: - providing refraction data of the eye for central vision; - providing biometric data of the eye comprising at least aberrations of the cornea of the eye; - providing a parametric eye model describing at least -- a corneal topography in the eye model; and -- positions of a plurality of points of a retina in the eye model by way of parameters of the eye model; - creating an individual eye model by adapting the parameters of the parametric eye model to the provided refraction data and biometric data of the eye of the spectacle wearer; and - determining the peripheral refraction data for the at least one eye of the spectacle wearer by calculating refraction data in the eye model for at least one instance of light incidence that deviates from central vision by a predetermined angle.

Description

[0001]Applicant: Rodenstock GmbH Our reference: R 3412WO - hb / hb Calculation of spectacle lenses taking peripheral refraction into account Description The present invention relates to improving the individual adjustment of at least one spectacle lens for efficient control of the development of myopia and good tolerability of the spectacle lens. The significant increase in the trend towards myopia in the population in recent years has, among other things, given rise to the development and manufacture of spectacle lenses, which aim to contribute to stopping or at least slowing down the progression of myopia in affected spectacle wearers. Several studies have shown that imaging on the peripheral (i.e. non-foveal) sections of the retina can play an effective role, provided this role is used appropriately.If peripheral light is not projected precisely onto the retina, but rather, for example, into a focus in front of the retina, this can slow the progression of myopia. Optical vision aids, particularly spectacle lenses, can exploit this effect. It has been shown that spectacle lenses with a radial increase in refractive power (radial refractive gradient, RRG), which, in contrast to conventional spectacle lenses, create a myopic defocus in the periphery and thus project the image in front of the peripheral retina, can slow the progression of myopia. However, due to the predominantly centrally sharp image, these RRG lenses encourage more head movements and are less tolerable. However, not every peripheral defocus is automatically a suitable means of combating myopia progression.On the one hand, a defocus appears to have a particularly beneficial effect when it is in front of the retina, and on the other hand, the quantitative distribution of the defocus across the retinal periphery also plays a role. The asymmetric retinal anatomy with regard to nasal and temporal regions (density of cones and ganglion cells) indicates a neurofunctional dominance of the nasal retina. Furthermore, it has been shown that myopia increases more rapidly when the retina is nasally and temporally symmetrical in terms of refractive power, and that myopia increases less when the retina shows asymmetric behavior in terms of shape and refractive power in the nasal-temporal region. Furthermore, there is evidence that the horizontal meridian has a dominant influence on the signal for the longitudinal growth of the eye and thus on the progression of myopia. For this reason, spectacle lenses have been developed and tested which only exhibit an increase in refractive power in the horizontal section and which is nasally / temporally asymmetric.However, such lenses do not take into account that peripheral refraction varies greatly from individual to individual. With a standard asymmetric design, a symmetrical refraction can arise from an already nasal / temporal asymmetric peripheral refraction, thus accelerating the progression of myopia. Therefore, it has been proposed to measure the peripheral refraction and take this into account when designing the asymmetry of the lens (e.g., WO 2017 / 222421 A1, WO 2020 / 229367 A1). Fig. 5A shows a schematic of the process: To measure a peripheral refraction, a visual angle ^^ is first determined in step ST110, at which the measurement is to be taken. In addition, it is possible to also determine an object distance to this visual angle in step ST110 (e.g., by ^^1 in diopters), which is practically often ^^1 = 0. A measuring process (ST120 in Fig.5A) then leads directly to the peripheral refraction value of 130. Such measurements can be performed for a wide variety of peripheral visual angles. This allows for highly reliable individual determination of peripheral refraction, and a corresponding customized spectacle lens for myopia control can be manufactured. However, this process is very complex. The optician / optometrist must have a suitable measuring device for measuring peripheral refraction, and the additional peripheral refraction measurements must also be performed individually. A further disadvantage of this approach is that these methods rely on conventional numerical optimization methods for spectacle lenses, which compare the light emanating from the spectacle lens to be optimized during the numerical calculation with the required individual peripheral refraction at the vertex sphere (i.e., without taking the biometry of the eye into account).WO 2018 / 138140 A3 describes methods that go beyond considering the vertex sphere and also take the individual biometry of the eye into account. However, these methods have so far only been able to consider central and not peripheral biometry. The object of the invention is therefore to improve the individual adjustment of at least one spectacle lens for efficient control of the development of myopia and good tolerability of the spectacle lens. This object is achieved by the invention defined in the independent claims. Preferred embodiments are the subject of the dependent claims. Thus, the invention relates in particular to a preferably computer-implemented method for determining individual prescription data for a spectacle wearer, which comprises peripheral refraction data for at least one eye of the spectacle wearer.The method comprises providing refraction data of the eye for central (i.e., foveal) vision. This refraction data is also referred to herein as central refraction data (of the real eye). This data can preferably be provided as aberrometry measurements on the eye of the spectacle wearer. The method further comprises providing biometric data of the eye, which at least comprise aberrations of the cornea of ​​the eye. This data can preferably be provided as keratometry measurements on the eye of the spectacle wearer. Furthermore, the method comprises providing a parametric eye model which describes at least -- a cornea topography in the eye model; and -- positions of a plurality of points of a retina in the eye model by parameters of the eye model, in particular including a central point and at least one peripheral point of the retina.In principle, any eye model is suitable that includes at least a defined optic and a retina with a fovea and at least one peripheral point such that ^ the eye model, using the defined optic, images a parallel beam of rays, including all aberrations, onto the fovea, leading to a defined PSF (point spread function) there and giving rise to defined aberrations; and ^ that an indication is given for peripheral imaging behavior due to the same optics, but in a different beam path. For this, the at least one additional point of the retina is required. In a simple embodiment, the eye model simply consists of a corneal surface, which, as in a reduced eye model, describes all the optical properties of the lens, as well as a distance from this surface to the retina. Further embodiments are all conceivable combinations of reduced eye models, e.g.with a cornea consisting of one surface and a lens consisting of one surface and two distances, etc. The Bennett-Rabbetts eye model with a cornea consisting of one surface and a lens consisting of two surfaces and three distances, or even more complex eye models, are also suitable eye models within the meaning of the invention. The parameters of the corresponding parameterized eye model are, in particular, the shapes (e.g., local inclinations and / or curvatures and / or surface refractive powers) and mutual distances between the surfaces. Furthermore, the method comprises generating an individual eye model by adapting the parameters of the parametric eye model to the provided refraction data and biometric data of the eye of the spectacle wearer, and determining the peripheral refraction data for at least one eye of the spectacle wearer by calculating refraction data in the individual eye model (i.e.,after individually adjusting the parameters of the parametric eye model) for at least one light incidence that deviates from central vision by a predetermined angle. The invention thus achieves several advantages over the prior art in that existing devices at the optician's, e.g. an aberrometer and topographer (e.g. DNEyeScanner), can be used. These allow the determination of central refraction by measuring the central aberrations. Preferably, the existing devices also measure the anterior chamber depth, and particularly preferably also the central and peripheral eye length. This makes it possible to set up an eye model with the help of which the peripheral refraction can be calculated without expensive additional devices or lengthy procedures.At the same time, the resulting eye model can later be used in the lens calculation to calculate the light emitted by the lens, taking into account the individual biometry of the eye, and then interpret it inside the eye with regard to defocus and other aberrations. The method according to the invention differs from the prior art not only in determining peripheral refraction without complex individual peripheral refraction measurements, but also in that a lens is calculated based on this measurement. The peripheral refraction influences how much the lens should perform to ensure the image is projected in front of the retina.The amount of additional peripheral refractive power, i.e. the forward displacement of the image in front of the peripheral retina, is preferably independent of the peripheral refraction itself and particularly preferably essentially constant, at least in some regions, and / or horizontally (i.e., temporal-nasal) asymmetric. Traditionally, high-quality, customized spectacle lenses are calculated / optimized for the viewing eye alone. This means that the eye rotates around the eye's pivot point in order to adopt different viewing directions, and then the calculation for each viewing direction is carried out peripherally by the spectacle lens but centrally by the (rotated) eye. This means that little changes in the eye (only pupil size, accommodation, etc.), but the central calculation remains through the eye.The oblique calculation through the eye to the peripheral retina is of no importance in conventional methods because it is assumed that visual acuity decreases dramatically there. In contrast, in a method according to the invention for calculating or optimizing a spectacle lens, the peripheral refraction data for at least one eye of the wearer are also taken into account by calculating and evaluating, in particular, an oblique (i.e. peripheral) incidence of light into the eye for at least part of the surface of the spectacle lens, in addition to or alternatively to a conventional calculation of a central image in the eye. For example, the eye could remain in its primary line of sight (looking straight ahead), while a peripheral incidence of light through the spectacle lens to be calculated or optimized and through the eye is calculated and evaluated. This could be done for the entire surface of the spectacle lens.Alternatively, in a preferred embodiment, a central region of the spectacle lens is evaluated in a conventional manner by incorporating calculations for the eye's central vision into a target function for this central region. In particular, this target function for the central region of the spectacle lens could exclusively consider the eye's central vision, as is done in conventional calculations or optimizations of individual spectacle lenses. Alternatively, it would also be possible to consider both the eye's central vision and peripheral vision in the target function for the central region of the spectacle lens.In yet another preferred embodiment, it would be possible to consider only terms of the eye's central vision in the target function for the central region of the spectacle lens, while for an intermediate region of the spectacle lens surrounding (and adjoining) the central region of the spectacle lens, both terms of the eye's central vision and terms of the eye's peripheral vision are considered in the target function. To consider both central and peripheral vision, one or more additional terms for peripheral vision (in particular with a corresponding weighting factor) could be considered for corresponding regions of the spectacle lens compared to a conventional target function (which only evaluates central vision). For example, a region with a radius or diameter of approximately 5 mm could be regarded as a central region of the spectacle lens.In a preferred embodiment, for a peripheral region of the spectacle lens (which, for example, corresponds to the points of vision through the spectacle lens for a gaze deflection of the eye above a minimum value, e.g. of 10 degrees), only terms of the peripheral vision of the eye are taken into account, i.e., within the scope of a calculation or optimization of a spectacle lens, only the angle through the eye is calculated for the peripheral region of the spectacle lens (while the eye, for example, remains in the primary direction of gaze). The spectacle lens is thus preferably optimized in the peripheral region only with regard to peripheral refraction. In comparison to a conventional objective function, no additional terms are taken into account in the objective function for this purpose, but conventional terms for evaluating central vision are replaced in the objective function by one or more terms for evaluating peripheral vision.Preferably, the provided central refraction data of the eye includes at least second-order aberrations, i.e., defocus and astigmatism. In a further preferred embodiment, the provided central refraction data of the eye also includes higher-order aberrations (e.g., coma and / or trefoil and / or spherical aberration and / or secondary astigmatism). This can further improve the quality of the spectacle lens to be calculated or optimized, since the determination of the peripheral refraction data and thus the peripheral calculation can then be carried out more precisely. Preferably, the provided biometric data of the eye also defines at least one central eye length and / or one central vitreous length of the eye, and preferably one or more peripheral eye lengths and / or vitreous lengths.Preferably, the parametric eye model also describes a position and effect of an eye lens through parameters of the eye model. In a preferred embodiment, the parametric eye model describes the positions of the plurality of points of the retina in the eye model using a model of the retina in the form of a sphere, the center of which lies on the optical axis of the eye model and which is tangent to or intersects the cornea in the eye model at least at one predetermined point. In a further preferred embodiment, the parametric eye model describes the positions of the plurality of points of the retina in the eye model using a model of the retina in the form of at least one ellipse.In a particularly preferred embodiment, the parametric eye model describes the positions of the plurality of retinal points in the eye model using a retinal model that parameterizes the nasal and temporal shape of the retina at least partially independently of one another. Preferably, determining the peripheral refraction data for the at least one eye of the spectacle wearer comprises determining at least one nasal and one temporal peripheral refraction.Preferably, determining the peripheral refraction data of the at least one eye for each peripheral ray direction from an object point to an image point on the retina of the individual eye model comprises determining an object-side wavefront of a spherical wave emanating from the object point at an evaluation surface of the eye model, determining an eye-side wavefront of a spherical wave converging at the image point on the retina at the evaluation surface, and evaluating a difference between the object-side and eye-side wavefronts at the evaluation surface as a value of the peripheral refraction data. For the purpose of evaluation, in particular, a corresponding metric for evaluating a comparison of wavefronts (in particular in a conventional manner) can be specified.In other words, preferably for each peripheral direction (each peripheral visual angle ^^ , or in two dimensions peripheral visual angle vector ^^ = (^^^^ , ^^^^) ), the peripheral refraction is calculated from the difference wavefront after defining a suitable metric, which is obtained in particular by substituting a spherical wave with radius ^̃^ from the wavefront ^^^^′. ^^^^ (^^) is subtracted, where ^̃^ ^^^^(^^) is the oblique distance along the oblique ray between the back surface of the lens and the retina and thus a characteristic of the direction ^^ and the geometry of the eyeball and in particular of the surface shape of the retina, and where ^^^^′ is the wavefront which results from the calculation of a spherical wavefront emanating from the object distance ^^1 used in refraction, which is calculated along the oblique peripheral ray through the eye model. In particular, a surface between the eye lens and the retina or another surface within the eye model can be used as the evaluation surface. It is also possible to use a surface outside the eye model, in particular in front of the eye model (e.g. the vertex sphere). Preferably, the method comprises specifying an object distance model which defines an associated object distance ^^(^^) for each (peripheral) ray direction (or viewing direction ^^).In a further aspect, the invention provides a method for calculating or optimizing a spectacle lens for a spectacle wearer, comprising: - determining individual prescription data for the spectacle wearer, which comprise peripheral refraction data for at least one eye of the spectacle wearer, according to one of the methods described here, in particular in one of the described, preferred embodiments; - specifying a parameterization of a first refractive surface and a second refractive surface for the spectacle lens to be calculated or optimized; - iteratively evaluating a target function and varying the parameterization of at least one of the refractive surfaces for the spectacle lens to be calculated or optimized in order to minimize the target function, wherein the target function is at least for a peripheral field of vision of the spectacle lens to be calculated or optimized.- evaluating the peripheral refraction data for at least one eye of the wearer contained in the individual prescription data; and - outputting the parameterization of the at least one varied, refractive surface resulting from minimizing the objective function. Thus, for the calculation or optimization of spectacle lenses, in particular as individually calculated or optimized (and then manufactured) spectacle lenses, it is desirable that the best possible correction of a refractive error of the wearer's eye is achieved for different viewing points of the spectacle lens. In general, a spectacle lens is considered fully corrective for a given viewing direction if the values ​​for the sphere, cylinder, and axis of the wavefront when passing the vertex sphere (or an alternative evaluation surface) agree with the values ​​for the sphere, cylinder, and axis of the prescription for the ametropia eye.When determining refraction for the eye of a spectacle wearer, dioptric values ​​(in particular sphere, cylinder, axial position - i.e. in particular sphero-cylindrical deviations) are determined for a far (usually infinite) distance and, if necessary (for multifocal or progressive lenses), an addition for a near distance (e.g. according to DIN 58208). These values ​​are intended to serve as the basis for the calculation or optimization (and thus for the production) of the spectacle lens. However, complete correction for all directions of vision simultaneously is not normally possible. Therefore, the spectacle lenses are manufactured in such a way that they provide good correction of refractive errors and only minor aberrations, especially in the main areas of use, especially in the central viewing areas, while larger aberrations are permitted or even deliberately placed in peripheral areas.In order to be able to manufacture a spectacle lens in this way, the lens surfaces or at least one of the lens surfaces is preferably first calculated in such a way as to achieve the desired distribution of the unavoidable and / or deliberately placed aberrations. This calculation and optimization is preferably carried out using an iterative variation method by minimizing an objective function. Unlike conventional objective functions, which only evaluate refraction data of the eye for central vision, this development proposes that the peripheral refraction data included in the individual prescription data and determined according to the invention be evaluated in the objective function using the objective function. Conventionally, for each visual point of the spectacle lens, it is assumed that there is a looking eye that looks directly (i.e. centrally) through the respective visual point.The eye's refraction data for this gaze direction are then compared in the objective function with a corresponding wavefront emanating from the associated object point and passing through the lens. This comparison results in a local evaluation of the lens, with the local evaluations of all visual points of the lens being summarized in the objective function. In the context of the present development, however, at least in part, for peripheral visual points of the lens, it is assumed that the eye does not look directly (i.e., centrally) through the respective peripheral visual point, but rather, for example, looks through a central visual point of the lens (central gaze direction) (for the purpose of the local evaluation of the respective peripheral visual point).The local evaluation of the respective peripheral visual point of the spectacle lens is carried out, in particular, at least partially by comparing the wavefront emanating from a corresponding object point and passing through the spectacle lens at this peripheral visual point with the peripheral refraction data of the eye. In a further aspect, the invention relates to a method for producing a spectacle lens, comprising: calculating or optimizing a spectacle lens according to the method for calculating or optimizing a spectacle lens in one of the embodiments described here; and manufacturing the spectacle lens thus calculated or optimized. The central region of the spectacle lens around the primary viewing direction (looking straight ahead) is preferably calculated / optimized for the viewing eye (direct vision with imaging onto the fovea).In this regard, a conventional procedure for formulating and evaluating an objective function (and its numerical, iterative minimization) can be used. Here, the calculation is preferably carried out straight and centrally through the eye. The provided refraction data for central vision is preferably taken into account. This area preferably includes at least the central visual point through the spectacle lens and, for example, a maximum area with a specified radius (e.g., no more than approximately 10 mm) around the central visual point. Outside of this area of ​​the spectacle lens there is an area which is calculated / optimized for peripheral vision (i.e., for the peripheral retina). This means that the calculation is carried out obliquely through the eye and the peripheral refraction, which is a function of the visual field angle, is taken into account.In addition to the determined peripheral refraction data, a plus power (additional positive dioptric power of the spectacle lens) is required to ensure that the image is formed in front of the peripheral retina. This additional positive power can have a value in a range of approximately 0.25 to approximately 5 dpt and can also depend on the visual field angle or vary nasally / temporally, but can also be constant. Another possibility is not to make an abrupt transition from direct central to peripheral vision, but to consider both types of terms in the calculation with a relative weighting (continuously changing across the lens). This means calculating both the ray path for the direct-looking eye and for the peripheral image when the eye is looking straight ahead. This is usually achieved by including both as a weighted term in the objective function.For the primary direction of gaze, the relative weight of the terms for central refraction is preferably 100% and for the terms for peripheral refraction (which can be a function of the visual field angle) preferably 0%. The relative weight for the terms for central refraction decreases outwards and for the terms for peripheral refraction increases outwards. From a predetermined transition line (between a central and a peripheral region of the spectacle lens) with a radial distance from the central viewing point of the spectacle lens of, for example, in a range of approximately 5 to approximately 20 mm, preferably approximately 10 mm, the relative weight of the terms for central refraction is 0% and the relative weight of the terms for peripheral refraction is 100%. Objective functions (error sum of squares) conventionally used for the calculation or optimization of a spectacle lens are often given by a sum of viewing angle-dependent terms ^^^^(^^^^, ^^^^), where. and where ^^^^ , ^^^^ are the coordinates of the evaluation points on the spectacle lens, and further exemplarily the residuals for astigmatism and refractive error (deviation actual value minus target value), weighted with weights ^^ ^^^^^^ ^^ (^^^^, ^^^^) and^^ ^^^^^^ ^^ (^^^^, ^^^^) construct the term ^^^^(^^^^, ^^^^), and where the sum runs over all evaluation points ^^. Furthermore, it contains ^^^^^^ ^^^^^^ ^^ ^^ ^^^^ ^^^^^^ ^^^^^^^^^^ ^^ ^^^^ the actual and Target values ​​for the refractive error and^^ ^^, ^^ , ^^ ^^, ^^ actual and target values ​​for the astigmatism. The coordinates ^^^^ , ^^^^ are clearly related to the viewing direction ^^^^ required to view the point ^^^^ , ^^^^. This conventional objective function ^^^^^^ ^^ is based on a looking eye. In contrast, within the scope of the present invention, an alternative objective function is preferably used ^^^^^^ ^^which is based in particular on an eye that is at rest or at least not moving across the entire field of view. In a preferred embodiment, the objective function ^^^^^^ ^^ An (essentially) resting eye, which always looks in the same direction of gaze, prefers the primary direction of gaze. For this purpose, a peripheral ray and wavefront calculation is incorporated into this objective function, whereby for each pair of coordinates ^^^^, ^^^^ (i.e., for each evaluation point of the lens), a term ^^^^(^^^^, ^^^^) according to ^^^^^^ 2 ^^ ^^ ^^^^^^ ^^ ^^^^^^ ^^^^^^^^ ^^ is evaluated, and for the entire lens a corresponding error sum of squares according to ^ ^^^^^ ^^ is formed. Here are ^^^^^^ ^^^^^^^^ (^^^^ , ^^^^), ^^^^^^ ^^^^^^^^^^ (^^^^, ^^^^) and ^^^^^^ ^^^^^^^^ (^^^^, ^^^^), ^^^^^^ ^^^^^^^^^^ (^^^^, ^^^^) are the actual and target values ​​for the refractive error and the astigmatism error of the resting eye. An example evaluation of the refractive error and astigmatism error using wavefront calculation will be presented later. To calculate or optimize a spectacle lens, either a pure objective function of the type ^^^^^^ ^^ or type ^^^^^^ ^^ be used. However, it is particularly preferable to combine these two objective functions to combine the advantages of both methods in a single lens. For example, the usual objective function for sharp vision can be maintained by adding both objective functions, but the objective function ^^^^^^ ^^for sharp central vision only for the central area of ​​the lens (e.g. within 5 mm or 10 mm radius around a central visual point) and the target function ^^^^^^ ^^ with defocus only outside. More generally, however, one can use a location-dependent weighted linear combination as the objective function, which is constructed, for example, by ^ ^^^^^ where in ^^^^(^^^^, ^^^^) and ^^^^(^^^^, ^^^^) are weights (ideally, but not necessarily ^^^^(^^, ^^) + ^^^^(^^, ^^) ≡ 1), which have a continuous excess between ^^^^^^^^ for central vision and ^^^^^^ ^^ in the periphery. Thus, a method for calculating or optimizing a spectacle lens for a spectacle wearer is preferably provided with an objective function ^^^^^^ according to ^ ^^^^^ for a plurality of viewing points (^^^^, ^^^^) of the spectacle lens, where ^^^^(^^^^, ^^^^) and ^^^^(^^^^, ^^^^) denote weighting factors for a term ^^^^(^^^^, ^^^^) of a looking eye for evaluating central refraction data and a term^^^^(^^^^, ^^^^) of a resting eye for evaluating the peripheral refraction data. Particularly preferred is the term ^^^^(^^^^, ^^^^) of a looking eye for evaluating the central refraction data according to ^ ^^ ^^ ^^ 2 ^^^^^ ^^ ^^^^^^ ^^^^^^^^ with weighting factors ^^ ^^^^^^ ^^ (^^^^, ^^^^) and ^^ ^^^^^^^^ (^^^^, ^^^^) for the evaluation of the deviations of the actual values ​​^^^^^^ ^^^^^^ ^^ (^^^^, ^^ ^^^^^^^^^^) of target values ​​^^^^^^^^ (^^^^, ^^^^) for the spherical refraction component of central vision or for the evaluation of the deviation of the actual values ​​^^^^^^ ^^^^^^^^ (^^^^, ^^^^) of target values ​​^^^^^^ ^^^^^^^^^^ (^^^^, ^^^^) for the astigmatic refraction component of central vision is evaluated. Alternatively or additionally, the term ^^^^(^^^^ , ^^^^) of a resting eye is preferably used to evaluate the peripheral refraction data according to ^^^ ^^^^^^ ^^ ^^ ^^^^^2 ^^ ^^ ^ ^ ^^ ^^ ^^ ^^^^^^ ^^^^^^^^ ^^ ^^ with weighting factors ^^ ^^^^^^ ^^ (^^^^, ^^^^) and ^^ ^^^^^^^^ (^^^^, ^^^^) for the evaluation of the deviations of the actual values ​​^^^^^^ ^^^^^^ ^^ (^^^^, ^^^^) of target values ​​^^^^^^ ^^^^^^^^^^ ^^ ^^^^ for the spherical refraction component of peripheral vision or for the deviation of the actual values ​​^^^^^^ ^^^^^^ ^^ (^^^^, ^^^^) of target values ​​^^^^^^ ^^^^^^^^^^ ^^ ^^^^ for the astigmatic refraction component of peripheral vision In a further preferred embodiment, the weighting factor ^^^^(^^^^, ^^^^) is set equal to zero for a central viewing area of ​​the spectacle lens, which in particular comprises a circular area with a radius of 5 mm. Alternatively or additionally, the weighting factor ^^^^(^^^^, ^^^^) is preferably set unequal to zero, in particular greater than the weighting factor ^^^^(^^^^, ^^^^) for at least a part of a peripheral viewing area of ​​the spectacle lens. In the methods described in this application, one or more or all steps can be computer-implemented, i.e., executed entirely by a computer or partially with the involvement of a computer. In particular, the provision of data can be carried out by means of a data carrier or by means of electronic (wired or wireless) data transmission, each via a suitable data interface. The determination, calculation, or optimization of variables can be carried out by means ofa processor of the computer. The computer can have corresponding modules in software or hardware, which have the instructions or circuits to carry out the steps. In a further aspect, the invention relates to a spectacle lens produced according to the method according to the invention. The spectacle lens can additionally have a mirroring or anti-reflective coating, a hard lacquer layer, a photochromic layer and / or a dirt-repellent layer. Furthermore, the spectacle lens can be machined or ground at the edge in order to accommodate the spectacle lens in a spectacle frame to form spectacles. In a further aspect, the invention provides a device for determining individual prescription data for a spectacle wearer, which comprises peripheral refraction data for at least one eye of the spectacle wearer, wherein the device comprises: - a data interface for acquiring refraction data of the eye forcentral vision; - a data interface for capturing biometric data of the eye, which at least includes aberrations of the cornea of ​​the eye; - a model module for providing a parametric eye model, which at least -- describes a cornea topography in the eye model; and -- positions of a plurality of points of a retina in the eye model using parameters of the eye model; - an adaptation module for generating an individual eye model by adapting the parameters of the parametric eye model to the provided refraction data and biometric data of the eye of the spectacle wearer; and - a determination module for determining the peripheral refraction data for the at least one eye of the spectacle wearer by calculating refraction data in the eye model for at least one light incidence deviating from the central vision by a predetermined angle. Preferably, the device for determining individual prescription data for a spectacle wearerdesigned to carry out a method for determining individual prescription data for a spectacle wearer in one of the preferred embodiments described here. In a further aspect, the invention relates to a device for calculating or optimizing a spectacle lens for a spectacle wearer, comprising: - a data interface for capturing individual prescription data for the spectacle wearer, which comprises peripheral refraction data for at least one eye of the spectacle wearer; - an optimization module which is designed to: -- specify a parameterization of a first refractive surface and a second refractive surface for the spectacle lens to be calculated or optimized; -- iteratively evaluate a target function and vary the parameterization of at least one of the refractive surfaces for the spectacle lens to be calculated or optimized in order to minimize the target function, wherein the target function is at least for a peripheral field of vision of the spectacle lens to becalculating or optimizing a spectacle lens, evaluates the peripheral refraction data for at least one eye of the wearer comprised of the individual prescription data; and - an output interface for outputting the parameterization of the at least one varied, refractive surface resulting after minimizing the objective function. Preferably, the device for calculating or optimizing a spectacle lens is designed to carry out a method for calculating or optimizing a spectacle lens in one of the preferred embodiments described here. In a further aspect, the invention relates to a device for producing a spectacle lens, comprising: - a calculation or optimization module, which is designed to calculate or optimize the spectacle lens according to a method for calculating or optimizing a spectacle lens according to one of the embodiments described here; and - a manufacturing module or processing module, which is designedare to manufacture or finish the spectacle lens. In a further aspect, the invention relates to a computer program product which, when loaded and executed on a computer, is designed to carry out a method for determining individual prescription data for a spectacle wearer and / or a method for calculating or optimizing a spectacle lens according to one of the embodiments described here. Finally, the invention relates to a use of a spectacle lens calculated or optimized according to the method according to one of the embodiments described here and / or a spectacle lens manufactured according to a manufacturing method described here for compensating a myopic refractive error and / or for reducing the progression of myopia. The invention is further described below with reference to technical explanations and preferred embodiments with reference to the attached drawings. Therein: Fig. 1 shows a schematic representationan eye model with a ray path for calculating a peripheral refraction; Figs. 2 and 3 are schematic representations of a cross-section of an eye from above with examples of preferred embodiments of models for describing the shape of a retina in eye models for use in preferred embodiments of the invention; Fig. 4 is a schematic representation of a surface (as a refracting surface or wavefront) to illustrate a preferred coordinate transformation of local coordinate systems when calculating the peripheral refraction; Fig. 5A is a flowchart to illustrate a conventional determination of peripheral refractions by direct measurement; Fig. 5B is a flowchart to illustrate an exemplary process for determining individual prescription data according to a preferred embodiment of the invention; and Figure 6 is a flowchart to illustrate an exemplary process for calculating peripheralRefraction data from an individual eye model in a method for determining individual prescription data according to a preferred embodiment of the invention. To achieve this object, the invention utilizes the fact that aberrations can be calculated during the oblique passage of a given incident wavefront ^^^^ along a peripheral ray through an individually defined eye model. The aberrations effective for the imaging can be determined as a result of the oblique passage of light through the optics of the eye in conjunction with the oblique distance traversed ^̃^ ^^^^from the posterior surface of the eye lens to the retina (see Fig. 1). Peripheral refraction is then again a special case of this situation, in which the incident wavefront is a spherical wave with object distance ^^1 (in dpt), with the preferred case of distance refraction being characterized by ^^1 = 0. The effective aberrations due to the effect of a spectacle lens are then to be calculated accordingly by using the wavefront exiting the spectacle lens as the incident wavefront ^^^^. For each peripheral direction (each peripheral visual angle ^^, or in two dimensions peripheral visual angle vector (visual direction vector ^^ = (^^^^, ^^^^) )), the oblique light passage results in a separate peripheral ray, and for each incident wavefront^^^^ at the posterior surface of the eye lens, a separate wavefront ^^^^′(^^^^, ^^) with individual aberrations (in the case of refraction determination ^^^^′(^^1, ^^) ). The oblique distance ^̃^ ^^^^(^^) is a characteristic of the direction ^^ and the geometry of the eyeball, in particular the surface shape of the retina. The comparison of the wavefront ^^^^′(^^^^, ^^) and the oblique distance ^̃^^^^^(^^) then results in a peripheral refraction as a function of ^^ and ^^^^. Even without direct measurement of the peripheral refraction, the invention therefore makes it possible to exploit the fact that the peripheral refraction can be calculated using a biometric eye model (i.e., in particular, a parametric eye model whose parameters are individually adapted). For example, if the shape of the cornea and the lens, as well as the anterior chamber depth and the lens thickness, are known from a model or a topography measurement up to a certain distance from the central ray (along the optical axis), an off-axis calculation of the wavefront of the light beam passing obliquely through the optics of the eye can be performed up to this distance using the individual eye model.In order to determine the peripheral refraction based on this, information about the oblique distance ^̃^ is also required. ^^^^between the lens of the eye and the retina. The process is shown schematically in Fig. 5B. The direct occurrence of peripheral refraction in Fig. 5B is again shown, but unlike in Fig. 5A, now with dashed lines to indicate that this alternative procedure is to be replaced according to the invention by the methods shown with solid lines, in particular with solid thick frames for the aberrometer measurement used according to the invention. The peripheral refraction is shown here as a combination of the wavefront ^^^^′(^^^^, ^^) and the oblique distance ^̃^^^^^(^^). The wavefront ^^^^′(^^^^, ^^) results after setting the parameters ^^,^^^^ by oblique calculation through the optics of the eye model. This, in turn, can be constructed from the aberrometry values ​​and the keratometry values ​​of the eye (see, for example, WO 2013 / 104548 A1).Subjective refraction preferably plays a role in verifying or improving the second-order aberrometry values ​​(defocus, astigmatism). The individual aberrometry values ​​and the individual keratometry values ​​are preferably obtained through direct measurement. In an alternative embodiment of the method, however, they can also be obtained (derived) based on subjective refraction, preferably using AI methods. The oblique distance ^̃^. ^^^^ (^^) does not arise independently of the optics of the eye model, because it is a characteristic of the position and direction of the image-side oblique ray in the vitreous body, which result as a function of ^^ after refraction by the components of the eye (especially the corea and the crystalline lens). In addition to the information of the ray parameters, information about the positions of a large number of points on the retina is also taken into account in order to ^̃^ ^^^^(^^) to be calculated. For the implementation of the present invention, the position of the plurality of points of the retina can be described using an eye model that draws on known models of the eyeball. The eye model can therefore be constructed using information from the literature or using AI methods from information about, for example, the visual impairment. Alternatively, the position of the retina can be described according to the invention using a model for the surface shape of the retina. The central distance of the retina from the eye lens, i.e., the vitreous depth, can in this case be taken from the eye model. The shape of the retina, in turn, can be constructed using information from the literature or using AI methods from information about, for example, the visual impairment. In a preferred embodiment of the invention, central biometer measurements are available; in a particularly preferred embodiment, central and peripheral biometer measurements are available (right side in Fig. 5B).A central biometer measurement can be used, for example, to measure the central length parameters of the eye and use them in the construction of an improved eye model. In particular, the measurement of length parameters (eye length, anterior chamber depth, etc.) can be performed as a central biometer measurement. If a peripheral biometer measurement is also available, then, in the case of many measurement points for different directions ^^, the function ^̃^ can be derived. ^^^^(^^) can be modeled directly, for example by linear interpolation or higher-order interpolation. If, on the other hand, only a few measurement points are available, or even just a single one, then this can be exploited in conjunction with a model of the eyeball by adjusting its model parameters. If measurements of peripheral refraction are still available to a limited extent, even if their necessity should be overcome by an aspect of the invention, then these can be exploited, for example to further improve the model for the shape of the retina and / or the eyeball. Fig. 5B therefore shows the possibility of using a measurement of peripheral refraction that is available for at least one peripheral direction to adapt the model (dashed in Fig. 5B). The steps in Fig. 5B are examples and can also be combined to form processes for which no arrow is explicitly shown. The steps from Fig.5B are described in detail below. Eye model A parametric eye model usable within the scope of the invention preferably describes at least - the topography of an anterior surface of the cornea; - the position and effect of a lens; and - the positions of a plurality of points of the retina, including a central point and at least one peripheral point of the retina. The eye model can, for example, also describe diffractive elements such as in an IOL or GRIN components (as a model of the human eye lens). The eye model preferably comprises sections of homogeneous media between ^^ refractive surfaces. An eye model as defined by WO 2013 / 104548 A1 can be used with particular preference. In this preferred case, ^^ = 3 and the refractive surfaces are the cornea, the anterior surface of the lens, and the posterior surface of the lens. Description of the peripheral ray, determination of its image-side ray To define the peripheral ray ^^. ^^In two dimensions, the object-side section of the ray can be described by the line of sight ^^. In three dimensions, an alternative way to parameterize the object-side ray mean of two angles ^^ = (^^^^, ^^^^) is, for example, a parameter representation of the position vector ^^ = (^^, ^^, ^^)^^ as a function of a straight line parameter^^(^^) = ^^0 + ^^^^ (1)where ^^ = (^^ , ^^ , ^^ ) ^^ is the starting point^^ 00 0 0 nkt and ^^ = (^^^^, ^^^^, ^^^^) is the direction vector. The direction vector ^^ is preferably a unit vector. This ray strikes the first refracting surface of an eye model, i.e. the cornea, is refracted there and propagates further within the eye model. By direct propagation and refraction of the beam through the components of the eye model, all subsections of the beam can be calculated numerically one after the other.In the case of the preferred eye model with partially homogeneous media between ^^ refracting surfaces, the ray description includes a total of ^^ intersection points ^^(^^) ^^ , 1 ≤ ^^ ≤ ^^ and (^^ + 1) direction vectors ^^(^^) ^^ , 0 ≤ ^^ ≤ ^^ . In a preferred description of the object-side ray, ^^ = ^^(1) (0) ^^ and ^^ = ^^^^. The prerequisite is that. optical components of the eye with regard to arrow height and 1st derivative, ie (local) position and inclination, are known with sufficient accuracy, at least at the position of the respective penetration points ^^(^^) ^ ^. The image-side section of the beam can then be described by the representation ^^′(^^′) = ^^′0 + ^^′^^′ (2), where ^^′0 = (^^′0, ^^′0, ^^′0) ^^ is the starting point and ^^′ =^^ ^^′^^, ^^′^^)^^ is the direction vector. Preferably, the direction vector ^^′ is a In a preferred description of the image-side beam, the starting point ^^′0 is then chosen so that it lies on the back surface of the eye lens, ie ^^′ = ^^ (^^) u (^^) 0^^ and ^^′ = ^^^^. As a result of the calculation, one obtains not only the direction vectors ^^(0) ^ ^ = ^^ and ^^(^^) ^^ = ^^′ , but also the direction vectors for all intermediate sections^^(1) ^^^^ ^^ (^^−1) ^ ^ (see Fig.6). Furthermore, all ^ ̃^ = ^^ (^^+1) − ^ (^^) ^^ ^^ ^^^ ^^ = ^^ − In a preferred embodiment, the peripheral ray is selected such that it passes through the center of the aperture stop of the eye model. Its calculation can be carried out by starting a ray in the center of the aperture stop in both the image-side and object-side directions, with the object-side and image-side directions then being directly obtained. However, if the direction of the object-side ray is to be predetermined instead, then an iteration preferably leads to the ray hitting the center of the aperture stop. Representation of the surfaces of the eye model adapted to the peripheral ray In the method according to the invention, the surface descriptions are normally available as a result of the measurement in a form related to a coordinate system centered around a fixed point that is independent of the peripheral ray calculation, for example around the optical axis (^^, ^^) = (0,0).For example, the cornea is represented either in a Zernike representation with respect to a pupil whose center is at (^^, ^^) = (0,0) or at another fixed point of the cornea (such as the apex), or in a Taylor representation centered around (^^, ^^) = (0,0) or the other fixed point. However, at least for a preferred case in which a symbolic calculation should be able to be carried out, each refracting surface ^^ is preferably represented as a Taylor representation in a coordinate system (^̃^, ^̃^, ^̃^) centered around the intersection point ^^(^^) ^. ^ is centered, and whose ^̃^ -axis is directed towards the and whose ^̃^ -axis is perpendicular to the plane of refraction (see Fig. 4). This allows for a symbolic calculation the direct application of the formalisms from G. Esser, et al. "Derivation of the refractive equations for higher order aberrations of local wavefronts by oblique incidence." J. Opt. Soc. Am. A 27, 218–237 (2010), G. Esser, et al. "Derivation of the propagation equations for higher order aberrations of local wavefronts" J. Opt. Soc. Am. A 28, 2442–2458 (2011) and W. Becken, et al. "Universal approach for local higher-order wavefront tracing equations for complex optical systems" J. Opt. Soc. Am. A 38, 1201– 1213 (2021).In other words, if the original surface description is in a coordinate system (^^, ^^, ^^) such that ^^ = ℎ(^^, ^^) describes the vertex, where ^^ℎ / ^^^^ = 0 and ^^ℎ / ^^^^ = 0 for (^^, ^^) = (0,0), then a coordinate transformation to a system (^̃^, ^̃^, ^̃^) must be used, for which ^̃^ = ℎ̃(^̃^, ^̃^) describes the vertex of the same surfaces centered around the intersection point (^^^^, ^^^^), where ^^ℎ̃ / ^^^̃^ = 0 and ^^ℎ̃ / ^^^̃^ = 0 for (^̃^, ^̃^) = (0,0), and where the point (^^ , ^^ , ^^ ) is generic for each possible intersection point (^^) ^^ ^^ ^^ dots ^^^^stands. A preferred parameterization of the coordinate transformation is ^^ ^^ ^^ ^̃^ where ^^ ^^^^ ^^ ^^^^ ^^ ^^^^ is an (orthogonal) rotation matrix that appropriately rotates the direction of the coordinate axes. This coordinate transformation is preferably applied to the coefficients of a Taylor representation up to a given order ^^^^^^ ^^^^^^ applied. The prerequisite is that all optical components of the eye are sufficiently accurate with regard to arrow height and all derivatives up to the order ^^^^^^ ^^^^^^ are known with sufficient accuracy, at least at the position of the respective intersection points ^^(^^) ^ ^ .If ^^20, ^^11, ^^02, ^^30, ^^21, ... are the Taylor coefficients of the area in the original system in the nomenclature according to EP 2710428 A1, and further ^̃^20, ^̃^11, ^̃^02, ^̃^30, ^̃^21, ... are the Taylor coefficients of the area in the transformed system, then ^̃^ 20 ^^ 20 ^^40(^^20, ^^11, ^^02, ^^30, ^^21, ^^12, ^^03) etc., where the remaining terms ^^ 30 , ^^ 21 , ^^ 12 , ^^ 03, ^^ 40 , … depend on terms of the incident wavefront whose order is at least 1 lower than the currently considered order, and where Oblique wavefront calculation Are the components of the eye model at the intersection points ^^(^^) ^ ^ sufficiently accurate up to a derivation of order ^^^^^^ ^ ^^^^^ known, then at these positions an off-axis calculation of the wavefront up to and including the higher order aberrations (HOA) of order ^^^^^^ ^^^^^^ be carried out. If the eye model is given in the preferred form by partially homogeneous media between ^^ refracting surfaces, then it is decisive that at all intersection points ^^(^^) ^^ , 1 ≤ ^^ ≤ ^^ the surfaces up to the respective derivative ^^^^^^ ^^^^^^are known. In one embodiment, this wavefront calculation is performed numerically using a beam of rays. A wavefront can then be fitted to the beam of rays, for example, in the form of a Taylor representation, or assuming a specific pupil using a Zernike fit. In another embodiment, this wavefront calculation is performed analytically once the beam calculation is available for all sections of the beam. For analytical calculations, state-of-the-art methods are preferably used (e.g. G. Esser, et al. "Derivation of the refractive equations for higher order aberrations of local wavefronts by oblique incidence." J. Opt. Soc. Am. A 27, 218–237 (2010), G. Esser, et al. "Derivation of the propagation equations for higher order aberrations of local wavefronts" J. Opt. Soc. Am. A 28, 2442–2458 (2011) and W. Becken, et al."Universal approach for local higher-order wavefront tracing equations for complex optical systems" J. Opt. Soc. Am. A 38, 1201–1213 (2021).). Preferably, an eye model is then used whose surfaces are described centered around the intersection points. For the wavefront calculation in the refraction determination, the initial wavefront ^^^^ is a spherical wave with radius 1 / ^^1, preferably a plane one (corresponding to ^^1 = 0). For the wavefront calculation in the general case, for example, when the wavefront ^^^^ originates from a spectacle lens, the wavefront can be specified arbitrarily. A preferred embodiment is shown in Fig. 6. The wavefront representation is first rotated onto a coordinate system whose z-axis is at the intersection point ^^(1) ^. ^ perpendicular to the refraction plane of the first refracting surface Then at the intersection point ^^(1) ^ ^ the refraction under oblique angle The incidence is calculated. Then the distance ^̃^ (1) propagated, and finally to the one for the refraction at the point ^^(2) ^ ^ appropriate coordinate system is rotated. After passing through the ^^ surfaces, a wavefront ^^^^′ results. Model for the shape of the retina of the eyeball If the real axial (or central) eye length ^^^^ =^^^^^^ + ^^^^ + ^^^^^^ (or the vitreous body length ^^^^^^, i.e., the distance between the lens and retina) is known at least in the central direction, then this value can be provided as part of the biometric data of the eye and taken into account when setting parameter values ​​in the parametric eye model to determine the individual eye model. For a given viewing direction ^^ and the resulting values ​​for the object-side viewing direction, one can then determine the oblique distance ^̃^ used within the scope of the invention. ^^^^Optionally, determine in particular by - model assumptions about the shape of the retina and subsequent geometric calculation - literature assumptions about the shape of the retina and subsequent geometric calculation - use of AI (Artificial Intelligence) methods to infer the shape of the retina from normal refraction and other parameters, followed by geometric calculation - direct peripheral measurement, e.g., using a biometer. If the real axial eye length ^^^^ or the vitreous length ^^ is also in the central direction ^^^^ of the real eye is not known, then the oblique distance used in the invention ^̃^ ^^^^optionally determined in particular by - model assumptions about the oblique distance as a function of the peripheral angle - literature assumptions about the oblique distance as a function of the peripheral angle - use of AI methods (Artificial Intelligence) to infer the oblique distance as a function of the visual direction ^^ from ordinary refraction and other parameters - direct measurement of the oblique distance as a function of the visual direction ^^, e.g. using a biometer. As an example of a preferred (parametric) model of the shape of the retina, a sphere is used whose radius corresponds to half the axial length (^^^^ / 2) (see 10a in Fig. 2), whose center lies in particular on the optical axis of the eye model and which is tangent to the cornea, especially at the corneal apex. This model of the shape of the retina is universally very easy to calculate and already produces quite good results in determining individual peripheral refraction data.As a further example of a preferred (parametric) model of the shape of the retina, a sphere is used whose radius is less than half the axial length (^^^^ / 2). In this case, in particular, the elevation with which the cornea protrudes forward from the eyeball is calculated out. For this purpose, in a preferred embodiment, the sphere is set such that its center lies on the optical axis of the eye model and it intersects the cornea (e.g., at approximately half its diameter) (10b in Fig. 2). In another preferred embodiment, the sphere for modeling the retina is set such that its center lies on the optical axis of the eye model and it intersects the cornea at its edge, preferably at a lateral distance of 6 to 7 mm from the corneal apex (10c in Fig. 2).As a further example of a preferred (parametric) model of the shape of the retina, an ellipsoid is used, the direction and length of the semi-axes of which can be adapted so that the curvature of the retina neither remains constant towards the periphery nor has a fixed value centrally. As a further example of a preferred (parametric) model of the shape of the retina, a conic section is used which touches the retina and has a given curvature at the point of contact (20). This curvature can be given by the curvature of the aforementioned sphere, for example 10a, preferably 10b, particularly preferably 10c). Preferably, the conic section describes an atorus, which can be adapted so that the curvature of the retina does not remain constant towards the periphery. This means, in particular, a surface that is neither rotationally symmetrical nor an exact sphere in every principal section.In each principal section, the curvature towards the periphery does not remain constant, but preferably follows the curve of a conic section. If the surface were otherwise rotationally symmetric, it would be an asphere. However, because it also has various principal sections, it is referred to here as an atorus. In a particularly preferred embodiment, the shape of the retina is modeled separately nasally and temporally, i.e., all previously mentioned conic sections (atorus or ellipsoid) appear in halved form nasally and temporally. The halved atori 20a and 20b then have different curvatures centrally for the nasal and temporal directions in the horizontal section, and the halved ellipsoids 21a and 21b do so accordingly. If only a few data points are available for the oblique distance or the shape of the retina (e.g.from two peripheral biometer measurements, one nasal and one temporal, preferably at 20°), then a model can be set up for the remaining directions by - linear interpolation from point to point - interpolation from point to point with higher order terms - linear regression - polynomial interpolation with higher order terms, whereby overfitting must be avoided - adaptation of the model parameters (i.e. semi-axes ^^ , ^^ , ^^ , the radius ^^ , conic constants ^^ of the conic section, etc.) of one of the above-mentioned models to the data An ellipsoid has the shape x - x 2 - 2 z - z 2. with semi-axes ^^ , ^^ , ^^ . Preferably, the ^^ -axis points in the direction of light, the retina is then described by the larger of the two solutions ^^(^^, ^^) (sign '+'). ^^0 = 0, ^^0 = 0 are preferred. An embodiment of an eyeball model is based on another representation of conic sections. A conic section in the xz-plane can also be described by ^ ^ ^^ 2 where ^^ is the radius of curvature at the vertex and ^^ is the conic constant. To create a retinal surface in space from the curve, one can, for example, rotate it around the z-axis and replace ^^2 in the conic equation with (^^2 + ^^2), thus creating a rotationally symmetric atoric surface: ^ ^ ^^ 2 +^^ 2 ^ ^^^ (12) Another possible description of the same area is obtained in polar coordinates^^ = ^^ ^^^^^^ ^^, ^^ = ^^ ^^^^^^ ^^: ^^ ^^ 2 ^ ^^^ To describe a non-rotationally symmetric surface, the parameters ^^ and ^^ can be functions depending on the azimuthal angle, which leads to the surface description ^ ^ ^^ 2 ^ ^^^ Preferably, the functions are given by an Euler transition: R= R cos 2 + 2 R sin cos j + R 2 yy sin j 2(15) cos j + k yy sin j In a further embodiment, an asymmetry between the nasal and temporal sides can be described. By convention, as in the right eye, the nasal side can be described by ^^ < 0 or by ^^ / 2 < ^^ ≤ 3^^ / 2, and the temporal side by ^^ ≥ 0 or 0 ≤ ^^ / 2 ≤ ^^ or 3^^ / 2 ≤ ^^ < 2^^. In the case of the ellipsoid, this means that instead of one semi-axis ^^, there are two parameters ^^ ^^^^^^ and ^^ ^^^^^^^^which represent the nasal and temporal sides, respectively. Accordingly, there are then two functions ^^^^^^^^,^^^^^^(^^, ^^) and ^^^^^^^^,^^^^^^^^(^^, ^^). In the case of the rotated conic section, instead of the two functions ^^(^^) and ^^(^^), there are two pairs of functions ^^^^^^^^(^^), ^^^^^^^^(^^) and ^^^^^^^^^^(^^), ^^^^^^^^^^(^^). Accordingly, there are then two functions ^^ (^^, ^ ^^^^,^^^^^^ ^) and . These should preferably be chosen so that the two halves fit together without an edge, i.e. so that ^^^^^^^^(^^, ^^) = ^^^^^^^^^^(^^, ^^) for ^^ = 0. While this is automatically the case in the case of the ellipsoid (more generally for ^^ = ^^0), in the case of the ator it must be required 22 In a particularly preferred embodiment, this is already fulfilled by R nas , yy =R temp , yy k (1 y y k 7) n as , = temp , yy Determination of the oblique distance ^̃^ ^^^^If the image-side ray is known, for example by specifying the parameters ^^′0, ^^′, and if the shape of the retina is known, then the point at which the image-side ray passes through the retina can be determined, and thus the oblique distance ^̃^ ^^^^ . This requires information about the position of the retina. If, as preferred, ^^′ is a unit vector and the starting point ^^′0 is on the posterior surface of the eye lens, then ^̃^^^^^ = ^^′ (18) where ^^′ describes the point of penetration through the retina. Peripheral refraction Peripheral refraction can be understood as a measure of the deviation of the wavefront ^^^^′ and the spherical wave, which has the radius ^̃^ ^^^^and which would produce a perfect image on the retina. This measure can be found once a suitable metric has been selected. In another embodiment, the peripheral refraction is given by the SZA values ​​of a wavefront in front of the eye, which, after peripheral wavefront calculation of the spherical wave through the eye for a given metric, results in the smallest possible deviations from the spherical wave with radius ^̃^ ^^^^ These SZA values ​​can be related to a corneal vertex distance HSA, preferably HSA=0. For example, when using an objective function already described above based on a resting eye with the term ^^^^^^ ^^^^^^ ^^^^^^^^2 The actual and target values ​​for the refractive error and the astigmatism error of the resting eye ( ^^^^^^ ^^^^^^(^^ , ^^ ), ^^^^^^ ^^^^^^^^(^^ , ^^ ) and ^^^^ ^^^^^^ ^^^^^^^^^^ ^^ ^^ ^^ ^^ ^^ ^^ ^^ (^^^^, ^^^^), ^^^^^^^^ (^^^^, ^^^^) ) can be determined by wavefront calculation. The actual values ​​are preferably determined by calculating a difference wavefront using a given metric, which is obtained by subtracting a spherical wave with radius ^̃^^^^^^(^^^^) from the wavefront ^^^^′(^^^^, ^^^^), where ^̃^ ^^^^ (^^ ^^ ) the oblique distance along the oblique between the and the retina and thus a feature of the direction ^^ ^^ The setpoints are preferably determined by physiological requirements, e.g. ^^^^^^ ^^^^^^^^ ^^ (^^^^ , ^^^^) = 0 , while ^^^^^^ ^^^^^^^^^^ (^^^^, ^^^^) is the defocus to be set for myopia prevention.

Claims

Applicant: Rodenstock GmbH "Lens calculation taking peripheral refraction into account" Our reference: R 3412 - hb / hb Patent claims 1. Method for determining individual prescription data for a spectacle wearer, which comprise peripheral refraction data for at least one eye of the spectacle wearer, the method comprising: - providing refraction data of the eye for central vision; - providing biometric data of the eye, which at least comprise aberrations of the cornea of ​​the eye; - providing a parametric eye model, which at least -- describes a cornea topography in the eye model; and -- positions of a plurality of points of a retina in the eye model using parameters of the eye model; - generating an individual eye model by adapting the parameters of the parametric eye model to the provided refraction data and biometric data of the eye of the spectacle wearer;and - determining the peripheral refraction data for the at least one eye of the spectacle wearer by calculating refraction data in the eye model for at least one light incidence deviating from the central vision by a predetermined angle.

2. The method according to claim 1, wherein the provided central refraction data of the eye comprise at least second-order aberrations.

3. The method according to claim 1 or 2, wherein the provided biometric data of the eye also define at least one central eye length and / or one central vitreous length of the eye and preferably one or more peripheral eye lengths and / or vitreous lengths.

4. The method according to one of the preceding claims, wherein the parametric eye model also describes a position and effect of an eye lens using parameters of the eye model.; 5. The method according to one of the preceding claims, wherein the parametric eye model describes the positions of the plurality of points of the retina in the eye model by a model of the retina in the form of a sphere, the center of which lies on the optical axis of the eye model and which is tangent to or intersects the cornea in the eye model.

6. The method according to one of the preceding claims, wherein the parametric eye model describes the positions of the plurality of points of the retina in the eye model by a model of the retina in the form of at least one ellipse.

7. The method according to one of the preceding claims, wherein the parametric eye model describes the positions of the plurality of points of the retina in the eye model by a model of the retina that parameterizes the shape of the nasal and temporal retina at least partially independently of one another. 8.Method according to one of the preceding claims, wherein determining the peripheral refraction data for the at least one eye of the spectacle wearer comprises determining at least one nasal and one temporal peripheral refraction.

9. Method according to one of the preceding claims, wherein determining the peripheral refraction data of the at least one eye comprises, for each peripheral ray direction from an object point to an image point on the retina of the individual eye model: - determining an object-side wavefront of a spherical wave emanating from the object point at an evaluation surface of the eye model; - determining an eye-side wavefront of a spherical wave converging at the image point on the retina at the evaluation surface; and - evaluating a difference between the object-side and eye-side wavefronts at the evaluation surface as a value of the peripheral refraction data.

10. A method for calculating or optimizing a spectacle lens for a spectacle wearer, comprising: - determining individual prescription data for the spectacle wearer, which comprise peripheral refraction data for at least one eye of the spectacle wearer, by a method according to one of the preceding claims; - specifying a parameterization of a first refractive surface and a second refractive surface for the spectacle lens to be calculated or optimized; - iteratively evaluating a target function and varying the parameterization of at least one of the refractive surfaces for the spectacle lens to be calculated or optimized in order to minimize the target function, wherein the target function is at least for a peripheral field of vision of the spectacle lens to be calculated or optimized.optimizing the spectacle lens, the peripheral refraction data included in the individual prescription data for the at least one eye of the spectacle wearer is evaluated; and - outputting the parameterization of the at least one varied, refractive surface resulting from minimizing the objective function.

11. The method according to claim 10, with an objective function ^^^^^^ according to: ^. ^^^^^ für eine Vielzahl von Durchblickspunkten (^^^^, ^^^^) des Brillenglases, wobei ^^^^(^^^^, ^^^^) und ^^^^(^^^^, ^^^^) Gewichtungsfaktoren für einen Term ^^^^(^^^^, ^^^^) zur Bewertung zentraler Refraktionsdaten und einen Term ^^^^(^^^^, ^^^^) zur Evaluation of peripheral refraction data.

12. Verfahren nach Anspruch 11, wobei der Term ^^^^(^^^^, ^^^^) zur Bewertung der central refraction data according to ^ ^^^^^ ^^^^^^ 2 ^ ^ ^^ ^^ ^^ ^^^^^^ ^^^^^^^^ with weighting factors ^^ ^^^^^^ ^ ^ (^^^^, ^^^^) und ^^ ^^^^^^ ^^ (^^^^, ^^^^) für die Bewertung der Deviations from the actual values ​​^^^^^^ ^^^^^^ ^^^^^^^^ ^^ (^^^^, ^^^^) von Soll-Werten ^^^^^^^^ (^^^^, ^^^^) für den spherical refraction component of central vision or for the evaluation of the deviation of the actual values ​​^^^^^^ ^^^^^^ ^^ (^^^^, ^^^^) von Soll-Werten ^^^^^^ ^^^^^^^^ ^^ (^^^^, ^^^^) für den astigmatic refraction component of central vision is evaluated; and / or w obei der Term ^^^^(^^^^, ^^^^) zur Bewertung der peripheren Refraktionsdaten according to ^ ^^^^^ ^^^^^^ ^ 2 ^ ^ ^^ ^^ ^^ ^^^^^^ ^^ ^^ ^^^^^^ ^^^^^^^ ^^ ^^ with weighting factors ^^ ^^^^^^ ^ ^ (^^^^, ^^^^) und ^^ ^^^^^^ ^^ (^^^^, ^^^^) für die Bewertung der Deviations from the actual values ​​^^^^^^ ^^^^^^ ^^ (^^^^, ^^^^) von Soll-Werten ^^^^^^ ^^^^^^^^ ^^ (^^^^, ^^^^) für den spherical refraction component of peripheral vision or for the evaluation of the deviation of the actual values ​​^^^^^^ ^^^^^^ ^^ (^^ ^^^^^^^^ ^^, ^^^^) von Soll-Werten ^^^^^^^^ ^^ ^^^^ für den astigmatic refraction of peripheral vision 13. Method according to claim 11 or 12, wherein for a central viewing area of ​​the spectacle lens, which in particular has a circular area with einem Radius von 5 mm umfasst, der Gewichtungsfaktor ^^^^(^^^^, ^^^^) gleich Null is set; and / or wherein for at least part of a peripheral Durchblicksbereichs des Brillenglases der Gewichtungsfaktor ^^^^(^^^^, ^^^^) ungleich Null, insbesondere größer ist als der Gewichtungsfaktor ^^^^(^^^^, ^^^^) gesetzt wird.

14. A method for producing a spectacle lens, comprising: calculating or optimizing a spectacle lens according to the method according to any one of claims 10 to 13; and manufacturing the thus calculated or optimized spectacle lens.

15. A spectacle lens produced according to the method according to claim 14.

16. A device for determining individual prescription data for a spectacle wearer, which comprises peripheral refraction data for at least one eye of the spectacle wearer, the device comprising: - a data interface for acquiring refraction data of the eye for central vision; - a data interface for acquiring biometric data of the eye, which at least includes aberrations of the cornea of ​​the eye; - a model module for providing a parametric eye model, which at least -- describes a cornea topography in the eye model; and -- positions of a plurality of points of a retina in the eye model using parameters of the eye model; - an adaptation module for generating an individual eye model by adapting the parameters of the parametric eye model to the provided refraction data and biometric data of the eye of the spectacle wearer;and - a determination module for determining the peripheral refraction data for at least one eye of the spectacle wearer by calculating refraction data in the eye model for at least one incident light that deviates from central vision by a predetermined angle.

17. A device for calculating or optimizing a spectacle lens for a spectacle wearer, comprising: - a data interface for acquiring individual prescription data for the spectacle wearer, which includes peripheral refraction data for at least one eye of the spectacle wearer; - an optimization module designed to: -- specify a parameterization of a first refractive surface and a second refractive surface for the spectacle lens to be calculated or optimized;-- iteratively evaluating an objective function and varying the parameterization of at least one of the refractive surfaces for the spectacle lens to be calculated or optimized in order to minimize the objective function, wherein the objective function is at least for a peripheral field of view of the lens to be; calculating or optimizing a spectacle lens, evaluates the peripheral refraction data for the at least one eye of the spectacle wearer, which are comprised in the individual prescription data; and - an output interface for outputting the parameterization of the at least one varied, refractive surface resulting after minimizing the objective function.

18. Device for producing a spectacle lens, comprising: - a calculation or optimization module for calculating or optimizing a spectacle lens according to the method according to one of claims 10 to 13; and - a manufacturing module for manufacturing the spectacle lens thus calculated or optimized.

19. Computer program product which, when loaded and executed on a computer, is designed to carry out a method according to one of claims 1 to 13.

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