Spectacle lens calculation taking into account peripheral refraction, method, device and computer program product

Abstract

The present invention relates to improving the individual adaptation of at least one spectacle lens for efficient control of myopia development and good lens tolerance. A method for determining individual prescription data for a spectacle wearer, comprising peripheral refraction data for at least one eye of the wearer, is proposed, wherein the method comprises: - Providing refraction data of the eye for central vision; - Providing biometric data of the eye, which includes at least aberrations of the cornea of ​​the eye; - Providing a parametric eye model that at least -- a corneal topography in an eye model; and -- describes the positions of a multitude 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 at least one eye of the spectacle wearer by calculating refraction data in the eye model for at least one light incidence that deviates from central vision by a given angle.

Description

[0001] The present invention relates to the improvement of the individual adaptation of at least one spectacle lens for efficient control of the development of myopia and good tolerability of the spectacle lens.

[0002] The significant increase in myopia among the population in recent years has prompted, among other things, the development and manufacture of spectacle lenses to contribute to halting or at least slowing the progression of myopia in affected spectacle wearers. Several studies have shown that imaging onto 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, especially spectacle lenses, can exploit this effect accordingly.It has been shown that lenses with a radial refractive gradient (RRG), which, unlike conventional 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 movement and are less comfortable to wear.

[0003] However, not every peripheral defocus is automatically a suitable means of combating myopia progression. Firstly, a defocus appears to have a particularly beneficial effect when it is located in front of the retina, and secondly, 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 and temporal regions. Furthermore, there is evidence that the horizontal meridian has a dominant influence on the signal for longitudinal growth of the eye and thus on the progression of myopia.

[0004] Therefore, lenses were developed and tested that exhibit an increase in refractive power only in the horizontal section, and that increase is nasally / temporally asymmetric. However, such lenses do not take into account the fact that peripheral refraction varies greatly from individual to individual. With a standard asymmetric design, a peripheral refraction that is already nasally / temporally asymmetric can sometimes become symmetrical, thus accelerating the progression of myopia.

[0005] Therefore, it has been proposed to measure the peripheral refraction and to take this into account when designing the asymmetry of the spectacle lens (e.g. WO 2017 / 222421 A1, WO 2020 / 229367 A1. In Fig. Figure 5A shows the process schematically: For the measurement of a peripheral refraction, a visual angle γ is first determined in step ST110, at which the measurement is to be made. Additionally, it is possible to also determine an object distance to this visual angle in step ST110 (e.g., by A1 in diopters), which is often A1 = 0. A measurement process (ST120 in Fig. 5A) then leads directly to the peripheral refraction value of 130. Such measurements can be performed for a variety of peripheral visual angles. This allows the peripheral refraction to be determined very reliably on an individual basis, 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 are based 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 biometrics of the eye into account).

[0006] WO 2018 / 138140 A3 describes methods that go beyond considering the vertex sphere and also consider the individual biometrics of the eye. However, these methods have so far only been able to consider central and not peripheral biometrics.

[0007] EP 4 232 272 B1 describes a method for producing a spectacle lens in which a coating is applied to a glass substrate, the surface of which is modified depending on a particularly peripheral refraction of a spectacle wearer.

[0008] 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 lens compatibility. This object is achieved by the invention defined in the independent claims. Preferred embodiments are the subject of the dependent claims.

[0009] Thus, the invention particularly relates to a method for determining individual prescription data for a spectacle wearer, which comprises peripheral refraction data for at least one eye of the 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 wearer.

[0010] The method further comprises providing biometric data of the eye, which includes at least aberrations of the cornea of ​​the eye. This data can preferably be provided as keratometry measurements on the eye of the spectacle wearer.

[0011] The method also comprises providing a parametric eye model which has at least -- a corneal topography in the eye model; and -- describes 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.

[0012] 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 • that the eye model, using the defined optics, projects a parallel beam of rays, including all aberrations, onto the fovea, resulting in a defined PSF (point spread function) and giving rise to defined aberrations; and • that there is evidence of peripheral imaging behavior due to the same optics but a different beam path. This requires at least one additional point on the retina.

[0013] In a simple embodiment, the eye model simply consists of a corneal surface which, as in a reduced eye model, describes all of 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 include, in particular, the shapes (e.g. local inclinations and / or curvatures and / or surface refractive powers) and mutual distances between the surfaces.

[0014] In addition, 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 the at least one eye of the spectacle wearer by calculating refraction data in the individual eye model (ie after individually adapting the parameters of the parametric eye model) for at least one light incidence deviating from the central vision by a predetermined angle.

[0015] 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 the 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 put on 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 eye model determined in this way can later be used in the spectacle lens calculation to calculate the light emanating from the spectacle lens, taking into account the individual biometry of the eye, and then to interpret it inside the eye with regard to defocus and other aberrations.

[0016] 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 spectacle lens is calculated based on this. Peripheral refraction influences how much the spectacle lens should achieve in order for the image to appear 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, at least in some regions, essentially constant and / or horizontally (i.e., temporal-nasal) asymmetric.

[0017] Traditionally, high-quality, custom lenses are calculated / optimized for the viewing eye alone. This means that the eye rotates around the ocular pivot point to adopt different viewing directions, and then, for each viewing direction, the calculation is performed peripherally through the lens but centrally through the (rotated) eye. This means that little changes in the eye (only pupil size, accommodation, etc.), but the calculation remains centrally through the eye. The oblique calculation through the eye to the peripheral retina is irrelevant in conventional methods, as it is assumed that visual acuity decreases dramatically there.

[0018] 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 as an alternative to a conventional calculation of a central image in the eye. For example, the eye could remain in its primary viewing direction (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 spectacle lens surface.

[0019] 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.

[0020] 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.

[0021] 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 allows the quality of the spectacle lens to be calculated or optimized to be further improved, since the determination of the peripheral refraction data and thus the peripheral calculation can then be carried out more precisely.

[0022] Preferably, 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.

[0023] Preferably, the parametric eye model also describes a position and effect of an eye lens through parameters of the eye model.

[0024] In a preferred embodiment, 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 whose center 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.

[0025] In a further preferred embodiment, 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.

[0026] In a particularly preferred embodiment, 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 which parameterizes the shape of the retina nasally and temporally at least partially independently of each other.

[0027] 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.

[0028] 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, a corresponding metric for evaluating a comparison of wavefronts can be specified (in particular in a conventional manner). In other words, preferably for each peripheral direction (each peripheral visual angle γ, or in two dimensions peripheral visual angle vector γ = (γ x , γ y)) the peripheral refraction is calculated from the difference wavefront after defining a suitable metric, which is obtained in particular when a spherical wave with radius d̃ is subtracted from the wavefront WF' LR (γ) is subtracted, where d̃ LR(γ) is the oblique distance along the oblique ray between the posterior surface of the lens and the retina and is thus a characteristic of the direction γ and the geometry of the eyeball and in particular of the surface shape of the retina, and where WF' is the wavefront that results from calculating a spherical wavefront emanating from the object distance A1 used during 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 that defines an associated object distance A(y) for each (peripheral) ray direction (or viewing direction y).

[0029] 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 evaluates the peripheral refraction data included in the individual prescription data for at least one eye of the wearer for at least one peripheral field of view of the spectacle lens to be calculated or optimized; and - Outputting the parameterization of the at least one varied refractive surface resulting from minimization of the objective function.

[0030] When calculating or optimising spectacle lenses, particularly when individually calculated or optimised (and then manufactured) spectacle lenses, it is desirable that the best possible correction of a refractive error in the wearer's eye is achieved for different viewing points of the lens. In general, a spectacle lens is considered fully corrective for a given direction of view if the values ​​for sphere, cylinder and axis of the wavefront as it passes the vertex sphere (or an alternative assessment surface) match the values ​​for 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 used for a long (usually infinite) distance and, if applicable (for multifocal lenses orProgressive lenses) an addition for a near distance (e.g. according to DIN 58208) is determined, which should serve as the basis for the calculation or optimization (and thus for the production) of the spectacle lens.

[0031] However, complete correction for all directions of vision simultaneously is usually not possible. Therefore, the lenses are manufactured in such a way that they provide good correction of refractive errors and only minimal aberrations in the primary areas of use, especially in the central viewing areas, while allowing or even deliberately placing more significant aberrations in peripheral areas.

[0032] In order to manufacture a spectacle lens in this way, the lens surfaces, or at least one of the lens surfaces, are 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 variational method by minimizing an objective function.

[0033] In contrast to conventional objective functions, which only evaluate the eye's refraction data for central vision, this development proposes that the peripheral refraction data contained in the individual prescription data and determined according to the invention be also 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 viewing direction is then compared in the objective function with a corresponding wavefront emanating from the associated object point and passing through the spectacle lens. This comparison results in a local evaluation of the spectacle lens, with the local evaluations of all visual points of the spectacle lens being summarized in the objective function.

[0034] In the context of the present development, however, the assumption is at least partially made for peripheral visual points of the spectacle lens 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 spectacle lens (central gaze direction) (for the purpose of 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.

[0035] 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 calculated or optimized spectacle lens.

[0036] The central region of the spectacle lens around the primary line of sight (looking straight ahead) is preferably calculated / optimized for the looking eye (direct vision with imaging onto the fovea). In this respect, 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 region preferably includes at least the central point of vision through the spectacle lens and, for example, a maximum region with a specified radius (e.g., no more than approximately 10 mm) around the central point of vision. Outside this region 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 performed 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 positive power (additional positive dioptric power of the lens) is required, which is intended to ensure that the image is formed in front of the peripheral retina. This positive additional power can range in value from 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.

[0037] 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 to each other (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 looks straight ahead. This is usually achieved by considering both as a weighted term in the objective function. For the primary gaze direction, 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) is preferably 0%. The relative weight for the terms for central refraction decreases towards the outside and for the terms for peripheral refraction increases towards the outside.From a given 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 the central refraction is 0% and the relative weight of the terms for the peripheral refraction is 100%.

[0038] Objective functions (error sum of squares) commonly used for the calculation or optimization of a spectacle lens are often given by a sum of viewing angle-dependent terms T b (x i , y i ), where FQSb=∑iTb(xi,yi) Tb(xi,yi)=gbref(xi,yi)(refbist(xi,yi)−refbsoll(xi,yi))2 +gbast(xi,yi)(astbist(xi,yi)−astbsoll(xi,yi))2 and where x i , y iare the coordinates of the evaluation points on the lens, and further, as an example, the residuals for astigmatism and refractive errors (deviation actual value minus target value), weighted with weights gbref(xi,yi) and gbast(xi,yi) the term T b (x i , y i ), and where the sum runs over all valuation points i. Furthermore, refbact(xi,yi),refbset(xi,yi) the actual and target values ​​for the refractive error and astbact(xi,yi),astbset(xi,yi) the actual and target values ​​for astigmatism. The coordinates x i , y i are clearly related to the viewing direction γ i together which is required to reach the point x i , y i This conventional objective function FQS b assumes a seeing eye.

[0039] In contrast, within the scope of the present invention, an alternative objective function FQS r 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 FQS describes b 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, where for each pair of coordinates x i , y i (ie for each evaluation point of the spectacle lens) preferably a term T r (x i , y i ) according to Tr(xi,yi)=grref(xi,yi)(refrist(xi,yi)−refrsoll(xi,yi))2 +grast(xi,yi)(astrist(xi,yi)−astrsoll(xi,yi))2 is evaluated, and for the entire lens a corresponding error sum of squares according to FQSr=∑iTr(xi,yi) is formed. Here are refrist(xi,yi),refrsoll(xi,yi) and astbist(xi,yi),astbsoll(xi,yi) The actual and target values ​​for the refractive error and astigmatism of the resting eye. An example evaluation of the refractive error and astigmatism using wavefront calculation will be presented later.

[0040] To calculate or optimize a spectacle lens, either a pure objective function of the type FQS b or type FQS r Particularly preferred, however, these two objective functions can also be combined 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 FQS bfor 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 objective function FQS r 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 FQS=∑i[gb(xi,yi)Tb(xi,yi)+gr(xi,yi)Tr(xi,yi)] where in g b (x i , y i ) and g r (x i , y i ) Weights are (ideally, but not necessarily g b (x, y) + g r (x, y) ≡ 1), which has a continuous excess between FQS b for central vision and FQS r in the periphery.

[0041] Thus, a method for calculating or optimizing a spectacle lens for a spectacle wearer is preferably provided with an objective function FQS according to FQS=∑i[gb(xi,yi)Tb(xi,yi)+gr(xi,yi)Tr(xi,yi)] for a variety of viewing points (x i , y i ) of the spectacle lens, where g b (x i , y i ) and g r (x i , y i ) Weighting factors for a term T b (x i , y i ) of a looking eye for the evaluation of central refraction data and a term T r (x i , y i ) of a resting eye for evaluating peripheral refraction data.

[0042] The term T is particularly preferred b (x i , y i ) of a looking eye to evaluate the central refraction data according to Tb(xi,yi)=gbref(xi,yi)(refbist(xi,yi)−refbsoll(xi,yi))2 +gbast(xi,yi)(astbist(xi,yi)−astbsoll(xi,yi))2 with weighting factors gbref(xi,yi) and gbast(xi,yi) for the evaluation of deviations from actual values refbist(xi,yi) of target values refbsoll(xi,yi) for the spherical refraction component of central vision or for the evaluation of the deviation of the actual values astbist(xi,yi) of target values astbset(xi,yi) for the astigmatic refraction component of central vision. Alternatively or additionally, the term T r (x i , y i ) of a resting eye to evaluate the peripheral refraction data according to Tr(xi,yi)=grref(xi,yi)(refrist(xi,yi))2+grast(xi,yi)(astrist(xi,yi)−astrsoll(xi,yi))2 with weighting factors grref(xi,yi) and grast(xi,yi) for the evaluation of deviations from actual values refbist(xi,yi) of target values refbsoll(xi,yi) for the spherical refraction component of peripheral vision or for the evaluation of the deviation of the actual values astbist(xi,yi) of target values astbset(xi,yi) evaluated for the astigmatic refraction component of peripheral vision.

[0043] In a further preferred embodiment, for a central viewing area of ​​the spectacle lens, which in particular comprises a circular area with a radius of 5 mm, the weighting factor g r (x i , y i ) is set equal to zero. Alternatively or additionally, the weighting factor g is preferably set for at least part of a peripheral viewing area of ​​the spectacle lens. r (x i , y i ) is not equal to zero, in particular greater than the weighting factor g b (x i , y i ) is set.

[0044] 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, the device comprising: - a data interface for collecting refraction data of the eye for central vision; - a data interface for collecting biometric data of the eye, which includes at least aberrations of the cornea of ​​the eye; - a model module for providing a parametric eye model, which at least -- a corneal topography in the eye model; and -- describes the 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 wearer's eye; 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 light incidence deviating from the central vision by a predetermined angle.

[0045] Preferably, the device for determining individual prescription data for a spectacle wearer is designed to carry out a method for determining individual prescription data for a spectacle wearer in one of the preferred embodiments described here.

[0046] 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 recording 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: -- 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 evaluates the peripheral refraction data included in the individual prescription data for at least one eye of the wearer at least for a peripheral field of view of the spectacle lens to be calculated or optimized; and - an output interface for outputting the parameterization of the at least one varied refractive surface resulting from minimization of the objective function.

[0047] 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

[0048] In a further aspect, the invention relates to a device for producing a spectacle lens comprising: - a calculation or optimization module 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 designed to manufacture or finish the spectacle lens.

[0049] 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.

[0050] 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.

[0051] The invention is further described below with technical explanations and preferred embodiments with reference to the attached drawings. In the drawings: Fig. 1 a schematic representation of an eye model with a ray path for calculating a peripheral refraction; Fig. 2 and Fig. 3 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 a schematic representation of a surface (as a refracting surface or wavefront) to illustrate a preferred coordinate transformation of local coordinate systems in the calculation of peripheral refraction; Fig. 5A is a flowchart illustrating a conventional determination of peripheral refractions by direct measurement; Fig. 5B is a flowchart illustrating an exemplary process for determining individual prescription data according to a preferred embodiment of the invention; and Fig. 6 is a flowchart illustrating an exemplary procedure for calculating peripheral refraction data from an individual eye model in a method for determining individual prescription data according to a preferred embodiment of the invention.

[0052] To achieve this objective, the invention utilizes the fact that aberrations can be calculated during the oblique passage of a given incident wavefront WF along a peripheral ray through an individually defined eye model. The aberrations effective for the image can be determined as a result of the oblique passage of light through the optics of the eye in conjunction with the oblique distance d̃ LRfrom the back surface of the lens to the retina (see Fig. 1).

[0053] Peripheral refraction is then again a special case of this situation, in which the incident wavefront is a spherical wave with object distance A1 (in dpt), whereby the preferred case of distance refraction is characterized by A1 = 0.

[0054] The effective aberrations due to the effect of a spectacle lens are then to be calculated accordingly by using the wavefront emerging from the spectacle lens as the incident wavefront WF.

[0055] For each peripheral direction (each peripheral visual angle γ, or in two dimensions peripheral visual angle vector (visual direction vector γ = (γ x , γ y))) the oblique light passage results in a separate peripheral ray, and for each incident wavefront WF at the posterior surface of the eye lens a separate wavefront WF'(WF, γ) with individual aberrations (in the case of refraction determination WF'(A1, γ)). The oblique distance d̃ LR (γ) is a characteristic of the direction γ and the geometry of the eyeball, in particular the surface shape of the retina. From the comparison of the wavefront WF'(WF, γ) and the oblique distance d̃ LR (γ) then results in a peripheral refraction as a function of γ and WF.

[0056] Even without direct measurement of peripheral refraction, the invention can therefore exploit the fact that peripheral refraction can be calculated using a biometric eye model (in particular a parametric eye model whose parameters are individually adapted). If, for example, 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 falling obliquely through the optics of the eye can be carried out up to this distance using the individual eye model. In order to determine the peripheral refraction based on this, information about the oblique distance d̃ LR between the lens of the eye and the retina.

[0057] In Fig. The process is shown schematically in Figure 5B. The direct occurrence of peripheral refraction on Fig. 5B is shown again, but different from 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.

[0058] The peripheral refraction is defined as a combination of the wavefront WF'(WF, γ) and the oblique distance d̃ LR(γ) is shown. The wavefront WF'(WF, γ) is determined after specifying the parameters γ, WF by oblique calculation through the optics of the eye model. This, in turn, can be constructed from the aberrometry and keratometry values ​​of the eye (see, for example, WO 2013 / 104548 A1). Subjective refraction preferably plays the role of verifying or improving the second-order aberrometry values ​​(defocus, astigmatism).

[0059] The individual aberrometry and 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.

[0060] The oblique distance d̃ LR(γ) 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 γ after refraction by the components of the eye (in particular corea and lens).

[0061] In addition to the information on the beam parameters, information on the positions of a large number of points on the retina is also taken into account in order to LR (γ) to be calculated.

[0062] To implement the present invention, the position of the numerous points on 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, refractive error.

[0063] Alternatively, the position of the retina can be described according to the invention using a model of the retina's surface shape. The central distance of the retina from the lens, i.e., the vitreous depth, can be taken from the eye model. The shape of the retina, in turn, can be constructed based on information from the literature or, using AI methods, from information about, for example, refractive error.

[0064] In a preferred embodiment of the invention, central biometer measurements are available, in a particularly preferred embodiment even central and peripheral (right side in Fig. 5B).

[0065] 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 used as a central biometer measurement.

[0066] If a peripheral biometer measurement is also available, then in the case of many available measuring points for different directions γ the function d̃ LR (γ) can be modeled directly, for example, by linear or higher-order interpolation. However, if only a few measurement points are available, or even just a single one, this can be exploited in conjunction with a model of the eyeball by adjusting its model parameters.

[0067] If peripheral refraction measurements are still available to a limited extent, even if their necessity is overcome by an aspect of the invention, then they 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 that a measurement of peripheral refraction, which is available at least for one peripheral direction, can be used to adapt the model (dashed in Fig. 5B).

[0068] The steps on Fig. 5B are examples and can also be combined to create processes for which no arrow is explicitly shown. The steps from Fig. 5B are described in detail below. Eye model

[0069] A parametric eye model usable within the scope of the invention preferably describes at least - The topography of a cornea; - Position and effect of a lens; and - Positions a plurality of points of the retina, including a central point and at least one peripheral point of the retina.

[0070] The eye model can, for example, also describe diffractive elements such as those in an IOL or GRIN components (as a model of the human eye lens). Preferably, the eye model comprises sections of homogeneous media between M refractive surfaces. An eye model as defined in WO 2013 / 104548 A1 can be used with particular preference. In this preferred case, M = 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 beam, determination of its image-side beam

[0071] To define the peripheral beam S p In two dimensions, the object-side section of the ray can be described by the viewing direction γ. In three dimensions, an alternative suitable way to parameterize the object-side ray is by means of two angles γ = (γ x , γ y ) for example a parametric representation of the position vector r = (x, y, z) Tas a function of a line parameter r(λ)=r0+λt where r0 = (x0, y0, z0) T the starting point and t = (t x , t y , t z ) T the direction vector. Preferably, the direction vector t is a unit vector.

[0072] 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. Through direct propagation and refraction of the ray through the components of the eye model, all subsections of the ray can be calculated numerically, for example. In the case of the preferred eye model with partially homogeneous media between M refracting surfaces, the ray description includes a total of M intersection points. rp(m),1≤m≤M and (M + 1) direction vectors tp(m),0≤m≤M In a preferred description of the object-side beam, r0=rp(1) and t=tp(0). The prerequisite is that all 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 rp(m).

[0073] The image-side section of the beam can then be represented by r′(λ′)=r′0+λ′t′ where r'0 = (x'0, y'0, z'0) T is the starting point and t' = (t' x , t' y , t' z ) T the direction vector. Preferably, the direction vector t' is a unit vector. In a preferred description of the image-side ray, the starting point r'0 is then chosen so that it lies on the back surface of the eye lens, ie r′0=rp(m) and t′=tp(M).

[0074] As a result of the calculation, one obtains not only the direction vectors tp(0)=t and tp(M)=t′ but also the direction vectors for all intermediate sections tp(1),tp(2),…,tp(M−1) (see Fig. 6). Furthermore, all distances between the penetration points d˜m=|rp(m+1)−rp(m)|, m=1,2,…,M−1

[0075] 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 achieved by launching 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 determined. However, if the direction of the object-side ray is to be specified instead, then an iteration preferably leads to the center of the aperture stop being hit. Representation of the surfaces of the eye model adapted to the peripheral ray

[0076] In the method according to the invention, the surface descriptions resulting from the measurement are normally available in a form related to a coordinate system centered around a fixed point independent of the peripheral ray calculation, such as the optical axis (x, y) = (0,0). For example, the cornea is represented either in a Zernike representation with respect to a pupil whose center lies at (x, y) = (0,0) or at another fixed point on the cornea (such as the apex), or in a Taylor representation centered around (x, y) = (0,0) or the other fixed point.

[0077] At least for a preferred case where a symbolic calculation should be possible, each refracting surface m is preferably represented as a Taylor representation in a coordinate system (x̃, ỹ, z̃) which is arranged around the intersection point rp(m) is centered, and whose z̃ -axis lies in the direction of the surface normal vector and whose x̃-axis lies perpendicular to the refraction plane (see Fig. 4). This allows 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) for a symbolic calculation.

[0078] In other words, if the original surface description is in a coordinate system (x, y, z) such that z = h(x, y) describes the sagittal height, where ∂h / ∂x = 0 and ∂h / ∂y = 0 for (x, y) = (0,0), then a coordinate transformation to a system (x̃, ỹ, z̃) has to be used, for which z̃ = h̃(x̃, ỹ) is the sagittal height of the same surfaces centered around the intersection point (x p , y p ), where ∂h̃ / ∂x̃ = 0 and ∂h̃ / ∂ỹ = 0 for (x̃, ỹ) = (0,0), and where the point (x p , y p , e.g. p ) generic for each possible penetration point rp(m) stands.

[0079] A preferred parameterization of the coordinate transformation is (xyh(x,y))=(xpyph(xp,yp))+R(x˜y˜h˜(x˜,y˜)) where R=(RxxRxyRxzRyxRyyRyzRzxRzyRzz) is an (orthogonal) rotation matrix that appropriately rotates the direction of the coordinate axes.

[0080] Preferably, this coordinate transformation is applied to the coefficients of a Taylor representation up to a given order ord max 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 ord max are known with sufficient accuracy, at least at the position of the respective penetration points rp(m).

[0081] Are a 20 , a 11 , a 02 , a 30 , a 21 , ... the Taylor coefficients of the area in the original system in the nomenclature according to EP 2 710 428 A1, and are further ã 20 , ã 11 , ã 02 , ã 30 , ã 21 , ... the Taylor coefficients of the area in the transformed system, then (a˜20a˜11a˜02)=RzzT2(R)(a20a11a02) (a˜30a˜21a˜12a˜03)=RzzT3(R)(a30a21a12a03)+(R30(a20,a11,a02)R21(a20,a11,a02)R12(a20,a11,a02)R03(a20,a11,a02)) (a˜40a˜31a˜22a˜13a˜04)=RzzT4(R)(a40a31a22a13a04)+(R40(a20,a11,a02,a30,a21,a12,a03)R31(a20,a11,a02,a30,a21 ,a12,a03)R22(a20,a11,a02,a30,a21,a12,a03)R13(a20,a11,a02,a30,a21,a12,a03)R04(a20,a11,a02,a30,a21,a12,a03)) etc., where the residual terms R 30 , R 21 , R 12 , R 03 , R 40 , ... depend on terms of the incident wavefront whose order is at least 1 lower than the currently considered order, and where T1(R)=(RxxRxyRyxRyy)T2(R)=(Rxx22RxxRyxRyx2RxxRxyRxyRyx+RxxRyyRyxRyyRxy22RxyRyyRyy2)T3(R)=(Rxx33Rxx2Ryx3RxxRyx2Ryx3Rxx2RxyRxx( 2RxyRyx+RxxRyy)Ryx(RxyRyx+2RxxRyy)Ryx2RyyRxxRxy2Rxy(RxyRyx+2Rx xRyy)Ryy(2RxyRyx+RxxRyy)RyxRyy2Rxy33Rxy2Ryy3RxyRyy2Ryy3)T4(R)=⋯ Oblique wavefront calculation

[0082] Are the components of the eye model at the penetration points rp(m) sufficiently accurate up to a derivation of the order ord max known, then an off-axis calculation of the wavefront up to and including the higher order aberrations (HOA) of order ord max If the eye model in the preferred form is given by partially homogeneous media between M refractive surfaces, then it is crucial that at all intersection points rp(m),1≤m≤M the areas up to the derivation ord max are known.

[0083] In one embodiment, this wavefront calculation is performed numerically using a beam of rays. A wavefront can then be fitted to the beam, for example, in the form of a Taylor representation or, assuming a specific pupil, using a Zernike fit.

[0084] In a further embodiment, this wavefront tracing is performed analytically as soon as the ray tracing is available for all sections of the ray. State-of-the-art methods are preferably used for the analytical tracing (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 used whose surfaces are described centered around the penetration points.

[0085] For wavefront calculations in refraction determination, the initial wavefront WF is a spherical wave with radius 1 / A1, preferably a plane wave (corresponding to A1 = 0). For wavefront calculations in the general case, for example, when the wavefront WF originates from a spectacle lens, the wavefront can be specified arbitrarily.

[0086] A preferred embodiment is shown in Fig. 6. The wavefront representation is first rotated to a coordinate system whose z-axis is at the intersection point rp(1) perpendicular to the refraction plane of the first refracting surface. Then, at the intersection point rp(1) the refraction under oblique incidence is calculated. Then the distance d̃ (1) propagated, and finally on the one for the refraction at the point rp(2) appropriate coordinate system. After passing through the M surfaces, a wavefront WF' results. Model for the shape of the retina of the eyeball

[0087] If at least in the central direction the real axial (or central) eye length AL = d CL + d L + d LR (or the vitreous body length d LR , i.e. the distance between the lens and the retina) is known, 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 γ and the resulting values ​​for the object-side viewing direction, one can then determine the oblique distance d̃ used in the invention. LR 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 ordinary refraction and other parameters, and by subsequent geometric calculation - direct peripheral measurement, e.g. using a biometer.

[0088] If the real axial eye length AL or the vitreous body length d is also in the central direction LR of the real eye is not known, then the oblique distance d̃ used in the invention can be LR optionally determine 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 (Artificial Intelligence) methods to infer the oblique distance as a function of the visual direction γ from ordinary refraction and other parameters - direct measurement of the oblique distance as a function of the viewing direction γ, e.g. using a biometer.

[0089] 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 (AL / 2) (see 10a in Fig. 2), whose center lies on the optical axis of the eye model and which touches the cornea, particularly at the corneal apex. This model of the shape of the retina is universally very easy to calculate and already yields quite good results in determining individual peripheral refraction data.

[0090] As a further example of a preferred (parametric) model of the shape of the retina, a sphere is used whose radius is smaller than half the axial length (AL / 2). In this case, in particular, the elevation with which the cornea protrudes forward from the eyeball is eliminated. 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) (Fig. 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 cornea apex (10c in Fig. 2).

[0091] As another example of a preferred (parametric) model of the shape of the retina, an ellipsoid is used whose direction and length of the semi-axes can be adjusted so that the curvature of the retina neither remains constant towards the periphery nor has a fixed value centrally.

[0092] As a further example of a preferred (parametric) model of the shape of the retina, a conic section is used that 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). The conic section preferably describes an atorus that 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 symmetric nor an exact sphere in every principal section. In every 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.

[0093] In a particularly preferred embodiment, the shape of the retina is modeled separately for the nasal and temporal directions, i.e., all of the aforementioned conic sections (atorus or ellipsoid) appear in halved form, both nasally and temporally. The halved atori 20a and 20b then have different central curvatures for the nasal and temporal directions in the horizontal section, and the halved ellipsoids 21a and 21b do the same accordingly.

[0094] 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 at preferably 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, where overfitting must be avoided - Adaptation of the model parameters (i.e. semiaxes a, b, c, radius R, conical constants κ of the conic section, etc.) of one of the above-mentioned models to the data

[0095] An ellipsoid has the shape 1=(x−x0)2a2+(y−y0)2b2+(z−z0)2c2zEH(x,y)=z0±c1−(x−x0)2a2−(y−y0)2b2 with semiaxes a, b, c. Preferably, the z-axis points in the direction of light; the retina is then described by the larger of the two solutions z(x,y) (sign , +'). Preferably, x0 = 0, y0 = 0.

[0096] An example of an eyeball model is based on another representation of conic sections. A conic section in the xz-plane can also be described by z(x)=x2R+R2−(κ+1)x2 where R is the radius of curvature at the vertex and κ 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 use x in the conic section equation. 2 by (x 2 + y 2 ) and thus create a rotationally symmetric atoric surface: zAt(x,y)=x2+y2R+R2−(κ+1)(x2+y2)

[0097] Another possible description of the same surface is obtained in polar coordinates x = r cos φ, y = r sin φ: zAt(r)=r2R+R2−(κ+1)r2

[0098] To describe a non-rotationally symmetric surface, the parameters R and κ can be functions depending on the azimuthal angle, which leads to the surface description zAt(r,φ)=r2R(φ)+R(φ)2−(κ(φ)+1)r2 leads.

[0099] Preferably, the functions are given by an Eulerian transition: R(j)=Rxxcos2j+2Rxysinj cosj+Ryysin2jk(j)=kxxcos2j+2kxysinj cosj+kyysin2j

[0100] In another 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 x < 0 or by π / 2 < φ ≤ 3π / 2, and the temporal side by x ≥ 0 or 0 ≤ π / 2 ≤ φ or 3π / 2 ≤ φ < 2π.

[0101] In the case of the ellipsoid, this means that instead of one semi-axis a, there are two parameters a nas and a temp which represent the nasal and temporal sides, respectively. Accordingly, there are then two functions z Ell,nas (x, y) and z Ell,temp (x, y).

[0102] In the case of the rotated conic section, instead of the two functions R(φ) and κ(φ), there are two pairs of functions R nas (φ), κ nas (φ) and R temp (φ), κ temp (φ). Accordingly, there are then two functions z At,nas (x, y) and zAt,temp (x, y).

[0103] Preferably, these should be chosen so that the two halves fit together without an edge, i.e. so that nas (x, y) = z temp (x, y) for x = 0. While this is automatically the case for the ellipsoid (more generally for x = x0), in the case of the atorus it must be required Rnas(j)+Rnas(j)2−(knas(j)+1)r2=Rtemp(j)+Rtemp(j)2−(ktemp(j)+1)r2

[0104] In a particularly preferred embodiment, this is already achieved by Rnas,yy=Rtemp,yyknas,yy=ktemp,yy Determination of the oblique distance d̃ LR

[0105] If the image-side ray is known, for example by specifying the parameters r'0, t', 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 d̃ LR. This requires information about the position of the retina. If, as preferred, t' is a unit vector and the starting point r'0 is on the back surface of the eye lens, then d˜LR=λ' where λ' describes the point of penetration through the retina. Peripheral refraction

[0106] Peripheral refraction can be understood as a measure of the deviation of the wavefront WF' and the spherical wave, which has the radius d̃ LR and which would produce a perfect image on the retina. This measure can be found once a suitable metric has been selected.

[0107] 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, with a given metric, lead to the smallest possible deviations from the spherical wave with radius d̃ LRThese SZA values ​​can be related to a corneal vertex distance HSA; preferably HSA=0.

[0108] For example, when using an objective function already described above FQSr=∑iTr(xi,yi) based on a resting eye with the term Tr(xi,yi)=grref(xi,yi)(refrist(xi,yi)−refrsoll(xi,yi))2 +grast(xi,yi)(astrist(xi,yi)−astrsoll(xi,yi))2 the actual and target values ​​for the refractive error and the astigmatism error of the resting eye (refrist(xi,yi),refrsoll(xi,yi) and astbist(xi,yi),astbsoll(xi,yi)) can be determined by wavefront calculation.

[0109] The actual values ​​are preferably determined by calculating a difference wavefront using a given metric, which is obtained by subtracting the wavefront WF' (WF, γ i ) a spherical wave with radius d̃ LR (γ i ) is subtracted, where d̃LR (γ i ) the oblique distance along the oblique ray between the back surface of the lens and the retina and thus a characteristic of the direction γ i is.

[0110] The target values ​​are preferably determined by physiological requirements, e.g. astrsoll(xi,yi)=0, while refrset(xi,yi) the defocus to be adjusted for myopia prevention.

Claims

[1] A 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 comprising: - Providing refraction data of the eye for central vision; - Providing biometric data of the eye, which includes at least aberrations of the cornea of the eye; - Providing a parametric eye model which has at least -- a corneal topography in the eye model; and -- Describes the positions of a plurality of points of a retina in the eye model using 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 wearer's eye; and - 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 light incidence deviating from the central vision by a predetermined angle. [2] The method of claim 1, wherein the provided central refraction data of the eye includes at least second-order aberrations. [3] Method according to claim 1 or 2, wherein the provided biometric data of the eye further 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] Method according to one of the preceding claims, wherein the parametric eye model further describes a position and effect of an eye lens by parameters of the eye model. [5] 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 whose center lies on the optical axis of the eye model and which is tangent to or intersects the cornea in the eye model. [6] 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] 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 which parameterizes the shape of the retina nasally and temporally at least partially independently of each other. [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 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. [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 evaluates the peripheral refraction data included in the individual prescription data for at least one eye of the spectacle wearer for at least one peripheral field of view of the spectacle lens to be calculated or optimized; and - Outputting the parameterization of the at least one varied refractive surface resulting from minimization of the objective function. [11] Method according to claim 10, with a target function FQS according to: FQS=∑i[gb(xi,yi)Tb(xi,yi)+gr(xi,yi)Tr(xi,yi)] for a variety of viewing points (x i , y i ) of the lens, where g b (x i , y i ) and g r (x i , y i ) Weighting factors for a term T b (x i , y i ) for the evaluation of central refraction data and a term T r (x i , y i ) for the evaluation of peripheral refraction data. [12] The method of claim 11, wherein the term T b (x i , y i ) for the evaluation of central refraction data according to Tb(xi,yi)=gbref(xi,yi)(refbist(xi,yi)−refbsoll(xi,yi))2 +gbast(xi,yi)(astbist(xi,yi)−astbsoll(xi,yi))2 with weighting factors gbref(xi,yi) and gbast(xi,yi) for the evaluation of deviations from actual values refbist(xi,yi) of target values refbsoll(xi,yi) for the spherical refraction component of central vision and for the evaluation of the deviation of the actual values astbist(xi,yi) of target values astbset(xi,yi) for the astigmatic refraction component of central vision; and / or where the term T r (x i , y i ) for the evaluation of peripheral refraction data according to Tr(xi,yi)=grref(xi,yi)(retrist(xi,yi)−refrset(xi,yi))2+grast(xi,yi)(astrist(xi,yi)−astrset(xi,yi))2 with weighting factors grref(xi,yi) and grast(xi,yi) for the evaluation of deviations from actual values refbist(xiyi) of target values refbsoll(xi,yi) for the spherical refraction component of peripheral vision and for the evaluation of the deviation of the actual values astbist(xi,yi) of target values astbset(xi,yi) for the astigmatic refraction component of peripheral vision is evaluated [13] Method according to claim 11 or 12, wherein for a central viewing area of the spectacle lens, which in particular comprises a circular area with a radius of 5 mm, the weighting factor g r (x i , y i ) is set equal to zero; and / or wherein for at least part of a peripheral viewing area of the spectacle lens, the weighting factor g r (x i , y i ) is not equal to zero, in particular greater than the weighting factor g b (x i , y i ) is set. [14] A method for producing a spectacle lens comprising: Calculating or optimizing a spectacle lens according to the method according to one of claims 10 to 13; and Manufacturing the calculated or optimized spectacle lens. [15] 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 collecting refraction data of the eye for central vision; - a data interface for collecting biometric data of the eye, which includes at least aberrations of the cornea of the eye; - a model module for providing a parametric eye model, which at least -- a corneal topography in the eye model; and -- Describes the 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 wearer's eye; 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 light incidence deviating from the central vision by a predetermined angle. [16] Device for calculating or optimising a spectacle lens for a spectacle wearer, comprising: - a device according to claim 15; - an optimization module designed to: -- 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 evaluates the peripheral refraction data included in the individual prescription data for at least one eye of the spectacle wearer for at least one peripheral field of view of the spectacle lens to be calculated or optimized; and - an output interface for outputting the parameterization of the at least one varied refractive surface resulting from minimization of the objective function. [17] 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 producing the calculated or optimized spectacle lens. [18] A computer program product which, when loaded and executed on a computer, is designed to carry out a method according to any one of claims 1 to 13.

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