DE102022209520A1 - OPHTHALMIC LENS AND METHOD FOR DESIGNING AND MANUFACTURING SAME - Google Patents

Abstract

An ophthalmic lens (10) with an extended focus range is provided, the ophthalmic lens (10) comprising a lens body (14) which has a plurality of concentrically arranged annular zones (12). Each of the annular zones (12) has a predetermined design refractive power, which differs from the respective design refractive powers of the directly adjacent annular zones (12). Each of the annular zones has (12) a topographic relief structure (16), which is designed to cause a phase shift (18) for a partial wave propagating through the respective annular zone (12), the phase shifts (18) being in the annular zones (12) at least partially differ from each other and each have one of at least five different predetermined values. Methods for designing and producing an ophthalmic lens (10) are also provided.

Description

Provided are an expanded focus range ophthalmic lens, a method of designing an ophthalmic lens, a method of manufacturing an ophthalmic lens, and use of a multiple annular zone division. The embodiments thus lie in the field of ophthalmic lenses and in particular in the field of intraocular lenses.

Ophthalmic lenses which have an extended focus range are known in the prior art. Such lenses are often referred to as EDOF lenses, which is an abbreviation for the English term “Enhanced Depth Of Field”, which refers to the extended focus range. Through an expanded focus range, it can be achieved in particular that ophthalmic lenses are accepted by the patient as a suitable visual aid even if the effect of the ophthalmic lens is not exactly adapted to the patient's ametropia or, in addition to long-distance vision, there is an additional continuous visual range an intermediate area and, if necessary, up to the close area is made possible.

Especially in the area of intraocular lenses, lenses are often used that have both a refractive and a diffractive effect, such as in EP 1 194 797 B1 described. Fresnel lenses with several zones are provided, in which the zones have the same zone areas according to the Fresnel division and in which an incoherent superposition of the partial waves takes place in the focus area, which are imaged by different zones of the Fresnel lenses. In particular, such lenses can be designed as bifocal or multifocal lenses. Conventional ophthalmic EDoF lenses, which are based on Fresnel lenses, typically have the disadvantage that diffractive effects arise at the zone boundaries, which reduce the imaging performance and lead to artifacts that can be perceived as disturbing. Conventionally, such diffractive effects are ignored or accepted as unavoidable. In addition, intraocular lenses are known in the prior art which have a diffractive structure with a periodicity of three zones, such as in EP2377493B1 described. EDoF lenses that do not have Fresnel profiles are also known in the prior art.

The task is therefore to provide an ophthalmic lens with an extended focus range which overcomes the disadvantages of conventional EDOF lenses.

The problem is solved by an ophthalmic lens with an extended focus range, a method for designing an ophthalmic lens, a method for producing an ophthalmic lens and a use of a division into several annular zones with the features of the respective independent claims. Optional refinements are specified in the subclaims and in the description.

In a first aspect, an ophthalmic lens with an extended focus range is provided. The ophthalmic lens comprises a lens body which has several concentrically arranged annular zones. Each of the annular zones has a predetermined design refractive power, which differs from the respective design refractive powers of the directly adjacent annular zones. In addition, each of the annular zones has a topographic relief structure which is designed to cause a phase shift for a partial wave propagating through the respective annular zone, the phase shifts in the annular zones being at least partially different from one another and each being one of at least five different predetermined ones have values.

In another aspect, a method of designing an ophthalmic lens is provided. The method includes determining a division of the ophthalmic lens into a plurality of concentrically arranged annular zones. The method further includes determining topographic relief structures for the annular zones such that the annular zones cause a phase shift for a partial wave propagating through the respective annular zone, the phase shifts in the annular zones at least partially differing from one another and each being one of at least five have different predetermined values.

In a further aspect, a method of producing an ophthalmic lens is provided. The method includes determining a division of the ophthalmic lens into a plurality of concentrically arranged annular zones. The method also includes determining topographical Relief structures for the annular zones such that the annular zones cause a phase shift for a partial wave propagating through the respective annular zone, the phase shifts in the annular zones at least partially differing from one another and each having one of at least five different predetermined values. In addition, the method includes producing the ophthalmic lens according to the specified subdivision and according to the specified topographic relief structures.

An ophthalmic lens is a lens that can be intended to correct a patient's ametropia. In particular, the ophthalmic lens can be designed as an intraocular lens. The ophthalmic lens can have a lens body, at least two optically effective surfaces and an optical axis.

An ophthalmic lens with an extended focus range is an EDoF lens. Due to their refractive and/or diffractive properties, such lenses can be designed to have a focus area that is larger than a focus area of a monofocal but otherwise similarly designed lens. In particular, ophthalmic lenses with an extended focus range can be designed as bifocal or multifocal lenses, with the addition refractive power of the foci being dimensioned such that a polychromatic extended focus range is created by superimposing the multiple foci.

The lens body is an optically active body that images the incident light to correct the patient's ametropia.

An annular zone is an annular zone which optionally extends concentrically around the apex on one of the surfaces of the ophthalmic lens and/or around the optical axis of the ophthalmic lens. No physical separation between adjacent annular zones is required. Rather, the annular zones can be separated or differentiated from one another by their respective topographic relief structures. An annular zone can have several subzones.

A design refractive power is a theoretical refractive and/or diffractive refractive power that can be assigned to a specific annular zone. This can also be referred to as the addition power. It is not necessary that the design refractive power of a single zone can be measured in isolation. Rather, a design refractive power can result from calculations and/or simulation data and can only serve to characterize the ophthalmic lens.

A topographic relief structure is a relief-like structure on a surface of the lens body, in particular on the front of the lens body. The topographic relief structure can have depressions and/or recesses and/or elevations relative to a base surface of the surface of the lens body and can be formed thereby. For example, the topographical relief structure can be introduced and/or applied to the lens surface by machining and/or can be produced with the lens during the production of the lens, for example in a casting process. The base area of the surface of the lens body is the surface shape that the surface of the lens body would have without the topographic relief structure. For example, the base surface can have a spherical and/or cylindrical shape or a free-form surface.

A phase shift is a change in the optical phase of a partial wave, which propagates through a topographic relief structure of a specific annular zone, compared to the phase of a reference partial wave. The reference wave can, for example, be the phase of a partial wave which propagates through an adjacent annular zone and/or a partial wave which propagates along the axial path and/or a partial wave which fictitiously propagates through the annular zone without the topographic relief structure.

A partial wave is a specific part of a light wave incident on the ophthalmic lens, which propagates through a specific annular zone. If the incident light wave covers several annular zones, several partial waves may be present.

A method for designing an ophthalmic lens refers to a method for creating parameters that characterize or define the ophthalmic lens and based on which the ophthalmic lens can be manufactured. The design can optionally be done on the basis of a computer simulation. Optionally, boundary conditions and/or parameters can be specified, by means of which the remaining parameters and the complete design for the ophthalmic lens are partially or completely automatically generated using a computer program.

The base surface is the surface course that the ophthalmic lens would have if no topographic relief structure were formed in or on it.

The disclosure offers the advantage that due to the at least partially different phase shifts of the partial waves, such periodicities in the phase front of the light wave imaged by the ophthalmic lens can be avoided or reduced, which can lead to unwanted and often disturbing interference effects. The disclosure can therefore avoid artifacts and thus improve the imaging performance of the ophthalmic lens and increase patient satisfaction.

Furthermore, by specifying the at least partially different phase shifts of the partial waves, the disclosure offers at least one further degree of freedom in the design of ophthalmic lenses, which can be used to adapt the properties of the ophthalmic lenses to the desired requirements.

Optionally, the phase shifts in the annular zones caused by the topographic relief structures are no more than twice a design wavelength. The design wavelength can be the design wavelength of 546 nm, or a wavelength range with a central wavelength of 546 nm ± 10 nm with a maximum width at half maximum (FWHM) of 20 nm, as in ISO 11979-2:2014 in section A.1 for Intraocular lenses specified. The fact that the phase shifts in the annular zones caused by the topographic relief structures are no more than twice a design wavelength is to be understood as relative to the phase of the wave front of the partial wave that the partial wave would have when propagating through the annular zone, if the topographic relief structure would not be present. The fact that the phase shifts are no more than twice the design wavelength enables a coherent addition of the phases and amplitudes of the partial waves in the focal area of the ophthalmic lens. This can improve the imaging performance of the ophthalmic lens.

The phase shifts in the annular zones caused by the topographic relief structures can differ from one another in pairs. This means that optionally all phase shifts caused by the topographic relief structures are different from all other phase shifts. In other words, the annular topographic relief structures cannot have identical relief structures, but rather each of the annular zones can have an individual topographic relief structure that differs from the relief structures of all other annular zones. This offers the advantage that undesirable interference effects, which can occur due to periodic topographic relief structures, can be avoided particularly effectively.

Alternatively, the phase shifts in the annular zones caused by the topographic relief structures can have a periodic distribution running radially outwards, provided that periodicity is avoided in a used area of the ophthalmic lenses, i.e. which is not regularly covered by the iris of the eye. In other words, there may be a periodicity with regard to the topographical relief structures, as long as this does not affect that part of the ophthalmic lens that develops the optical effect in the eye. Each of the annular zones may have a predetermined zone area. The predetermined zone areas of the annular zones can at least partially differ from one another. In other words, the topographic relief structures of the individual annular zones can differ in their respective zone area. This offers a degree of freedom through which the phase shifts can be easily influenced in the design of the ophthalmic lens.

The annular zones can each have one of at least two different predetermined zone areas and optionally one of at least five different predetermined zone areas. In particular, the predetermined zone areas of the plurality of annular zones can be different from one another in pairs. This can be particularly advantageous in that periodicities in the surface structure of the ophthalmic lens and thus in the phase fronts of the light wave or the partial waves can be avoided or reduced. A variation of the predetermined zone areas can be achieved by varying the zone widths. For example, the predetermined zone areas chen over the majority of the annular zones must be determined in such a way that they approximately follow a normal distribution.

The predetermined zone surfaces of adjacent annular zones can have a periodic distribution of the predetermined zone surfaces running radially outwards, provided that periodicity is avoided in a used area of the ophthalmic lenses, ie which is not regularly covered by the iris of the eye. In other words, there may be a periodicity with regard to the topographical relief structures, as long as this does not affect that part of the ophthalmic lens that develops the optical effect in the eye. At least one of the several annular zones and optionally all of the several annular zones can each have a main subzone and a phase subzone, such as in the publication EP 1 194 797 B1 described. The main subzone can primarily serve to effect the desired phase modulation within the zone and the phase subzone primarily serves to produce a phase shift relative to the adjacent main subzone and thereby optionally produce a continuous course of the surface of the ophthalmic lens. For example, the main subzone may occupy approximately 90% of the zone area of the annular zone and the phase subzone may occupy approximately 10% of the zone area of the annular zone. Optionally, the phase subzone can be designed in such a way that the phase subzone returns the topographical relief structure to the base surface of the ophthalmic lens, that is to say that the topographical relief structure at the border between two adjacent annular zones is returned to the level that the surface of the lens body is ignored corresponds to the topographic relief structure.

Alternatively or in addition to varying zone areas, the respective topographic relief structures of the annular zones can differ at least partially in their relief depth. The relief depth is an extent of the depression and/or elevation of the topographic relief structure perpendicular to the base surface, i.e. perpendicular to the surface of the lens body. The zone depth does not have to be the same over the entire topographic relief structure, but can have a course over the annular zone, in particular a relief depth that changes radially over the annular zone. The relief depth of a topographic relief structure can optionally have a rectilinear, parabolic, hyperbolic or circular arc-shaped course in the radial direction. Unless otherwise stated, relief depth is the maximum relief depth of an annular zone.

The topographic relief structures of the annular zones can each have one of at least two different predetermined relief depths, optionally one of at least five different predetermined relief depths and optionally one of at least five different predetermined relief depths. The predetermined relief depths of the topographic relief structures of the multiple annular zones can optionally be different from one another in pairs. This offers the possibility of providing the phase shifts caused by the topographic relief structures in a simple manner. Optionally, this can be combined with a variation of the zone areas of the annular zones. The predetermined zone areas of the several annular zones can optionally each lie in a range of 0.3 mm ² and 2 mm ² .

The zone areas of the annular zones can correspond to a random distribution. Likewise, the topographic relief depths of the annular zones can correspond to a random distribution. The random distribution can be based on a distribution function, such as a normal distribution or any other distribution function. The distribution function can be specified as a parameter for generating the random distributions. The random distribution can determine the individual deviations of the respective zone areas from a default value. For example, a Fresnel division can be used as a starting value, in which all annular zones of an ophthalmic lens have the same zone areas. By means of a random distribution, for example, variations of the individual zone surfaces can be determined in deviation from the Fresnel division in order to avoid, as described above, undesirable periodicities in the surface structure of the ophthalmic lens and the associated undesirable interference. Alternatively or additionally, a mean and/or median value for the zone areas and/or the relief depths can be specified as the initial value, on the basis of which the random distribution can then be used to vary the zone areas and/or relief depths.

The method for designing an ophthalmic lens can be designed in such a way that the topographical relief structures are determined in such a way that the phase shifts of the several annular zones caused by the topographical relief structures are different in pairs. However, a pairwise difference is not absolutely necessary for the advantages of the disclosure to arise. In particular, when using a random distribution, it can happen that two or Even several annular zones happen to have the same zone areas according to the random distribution, although the probability of this can be very low. This does not conflict with the fact that the aim of the random distribution is to avoid undesirable periodicities in the surface structure of the ophthalmic lens and in particular in the topographical relief structures.

The determination of the topographic relief structures and the zone areas can therefore be done on the basis of a random distribution. The determination of the topographic relief structures can include varying the respective zone areas of the annular zones based on predetermined initial values for the respective zone areas and/or varying the respective relief depths based on predetermined initial values for the respective relief depths. As described above, a distribution function, such as a normal distribution or a uniform distribution, can serve as the initial value. Alternatively or additionally, a desired mean value and/or median value can be specified for the relief depth. The predetermined initial values for the respective zone areas and/or relief depths can be predetermined in such a way that the initial values for the respective zone areas and/or respective relief depths correspond to a Fresnel division.

To determine a suitable random distribution, the method for designing an ophthalmic lens can optionally use a Monte Carlo simulation. The method may further include filtering the simulation results to identify those simulation results which lie within a desired parameter range that is expected to have suitable properties of the design for the ophthalmic lens. For example, one or more of the following parameters can be used as possible variation parameters and optimization variables: a number of annular zones, a type of distribution function for zone areas and/or additive refractive powers of the individual annular zones, a distribution function for the relief depths and/or the shape of the relief in the topographic relief structures, absolute phase shifts in the individual annular zones, and upper and/or lower starting points of the variation and equivalent parameters.

• Belsley, David A.: Generating Random Numbers in Mathematica 6, S. 71-77 . DOI: 10.10071978-1-4757-2644-2_5.
• H. Amman et al. (eds.), Computational Approaches to Economic Problems, 71-77; 1997, Kluwer Academic Publishers.

To generate a random distribution, for example, a random generator known from the prior art can be used, such as the random generator implemented as standard in the WOLFRAM MATHEMATICA 13.0.1 software. This is characterized by an extremely long periodicity and advantageous properties for generating random numbers according to certain distributions. Further details can be found in the following publications, for example:

• Belsley, David A.: Generating Random Numbers in Mathematica 6, pp. 71-77 . DOI: 10.10071978-1-4757-2644-2_5.
• H. Amman et al. (eds.), Computational Approaches to Economic Problems, 71-77; 1997, Kluwer Academic Publishers.

The features and embodiments mentioned above and explained below are not only to be viewed as disclosed in the combinations explicitly mentioned in each case, but are also included in the disclosure content in other technically sensible combinations and embodiments.

• 1 zeigt in einer schematischen Darstellung eine ophthalmische Linse gemäß einer optionalen Ausführungsform.
• 2 zeigt eine beispielhafte Illustration einer ophthalmischen Linse gemäß einer optionalen Ausführungsform in Querschnittsansicht.
• 3 erläutert anhand zweier Graphen eine ophthalmische Linse gemäß einer weiteren optionalen Ausführungsform.
• 4 zeigt in einem beispielhaften Graphen das Phasenprofil einer ophthalmischen Linse gemäß einer weiteren optionalen Ausführungsform.
• 5 zeigt ein topographisches Oberflächenprofil und ein Phasenprofil einer ophthalmischen Linse gemäß einer weiteren optionalen Ausführungsform.
• 6 zeigt das Oberflächenprofil und das Phasenprofil einer weiteren optionalen Ausführungsform einer ophthalmischen Linse.
• 7 erläutert beispielhaft ein Verfahren zum Designen einer ophthalmischen Linse gemäß einer optionalen Ausführungsform.
• Die 8A und 8B zeigen beispielhaft optional vorgegebene Verteilungsfunktionen.
• 9 zeigt beispielhaft eine Reihe von möglichen Zielfunktionen für die relative Abbildungsleistung eines Ziel-Designs.

Further details and advantages will now be explained in more detail using the following examples and optional embodiments with reference to the figures.

• 1 shows a schematic representation of an ophthalmic lens according to an optional embodiment.
• 2 shows an exemplary illustration of an ophthalmic lens according to an optional embodiment in a cross-sectional view.
• 3 explains an ophthalmic lens according to a further optional embodiment using two graphs.
• 4 shows in an exemplary graph the phase profile of an ophthalmic lens according to a further optional embodiment.
• 5 shows a topographical surface profile and a phase profile of an ophthalmic lens according to a further optional embodiment.
• 6 shows the surface profile and the phase profile of a further optional embodiment of an ophthalmic lens.
• 7 exemplifies a method for designing an ophthalmic lens according to an optional embodiment.
• The 8A and 8B show examples of optionally specified distribution functions.
• 9 shows an example of a number of possible target functions for the relative imaging performance of a target design.

In the following figures, the same or similar elements in the various embodiments are designated with the same reference numerals for the sake of simplicity.

1 shows a schematic representation of an ophthalmic lens 10 according to an optional embodiment in plan view, in which a plurality of annular zones 12 are formed on the lens body 14. The ophthalmic lens 10 can be designed as an intraocular lens and, in addition to the lens body 14, have further elements, such as one or more haptics, although these are not shown in the schematic representation. The annular zones 12 are arranged concentrically on the lens body 14 and accordingly have a ring-like shape, the size and width of the annular zones 12 being determined by an inner and an outer radius of the annular zone 12. The innermost zone Z1 has a circular disk shape, which is characterized by an inner radius equal to zero. All annular zones 12 from the second zone Z2, which are located radially further out, have a ring-like shape in which the inner radius is not equal to zero.

According to the embodiment shown, the annular zones 12 have different widths and zone areas. Unlike a Fresnel division, in which all zones have the same zone areas, according to the embodiment shown, the zone areas are varied in order to avoid a periodic structure on the surface of the ophthalmic lens 10. This makes it possible to avoid artifacts which could otherwise occur due to interference due to the periodic structure and which can reduce the imaging performance of the ophthalmic lens 10.

The lens body 14 can be made entirely of one material, so that there is no change in the volume of the lens body, particularly at the boundaries between adjacent annular zones 12. However, the annular zones can be distinguished by a topographic relief structure located on the surface of the ophthalmic lens. This will be exemplified below with reference to 2 explained.

2 shows an exemplary illustration of an ophthalmic lens 10 according to an optional embodiment in a cross-sectional view, in which the lens body 14 has a plurality of annular zones 12. It can be seen that the annular zones extend concentrically around the optical axis 1000 of the ophthalmic lens 10. On the upper surface of the lens, which in the case of an intraocular lens can be the surface that faces the iris, topographic relief structures 16 are attached, each of which extends in an annular zone 12 and correspondingly runs concentrically around the optical axis 1000. It should be noted that neither the number nor the size of the annular zones 12 and the topographical relief structures 16 are shown to scale, but for better visibility the number of the annular zones 12 is reduced and the expression of the topographical relief structures 16 relative to the lens body 14 is shown enlarged can.

The topographical relief structures 16 are designed in such a way that they provide the ophthalmic lens with a diffractive effect, which, together with the refractive effect of the lens body 14, shapes the optical effect of the ophthalmic lens 10.

According to the optional embodiment shown, the topographic relief structures 16 are each formed by a recess or depression in the lens body 14 opposite the regular surface of the lens body 14, which the lens body 14 would have without the topographic relief structures 16. The regular surface of the lens body 14 is also referred to as the base surface 14a in the context of this disclosure.

According to the optional embodiment shown, the individual annular zones 12 differ from one another in their zone areas and the topographic relief structures 16 differ from one another in their relief depth. The maximum height between the highest and lowest points of the topographic relief structure parallel to the optical axis 1000 or perpendicular to the base surface 14a is referred to as the relief depth. Due to the varying zone areas and the varying relief depths Phase shifts are generated, which collect individual partial waves that propagate through an annular zone 12, whereby the resulting phase shifts also differ from one another. By avoiding periodicities and in particular short periodicities, ie over only a few annular zones 12, the occurrence of undesirable interferences and artifacts can be avoided and the imaging performance of the ophthalmic lens 10 can be improved accordingly.

The annular zones 12 and the topographic relief structures 16 are optionally designed such that the phase shifts collected by the partial waves in the individual annular zones 12 do not each exceed a value of twice the design wavelength. In the case of an ophthalmic lens 10 designed as an intraocular lens, the design wavelength is optionally 546 nm, as specified in the ISO 11979-2 standard. This enables a coherent addition of the individual partial waves, i.e. the individual components of the light wave imaged by the individual annular zones 12 of the ophthalmic lens 10, in the focal area of the ophthalmic lens 10 and correspondingly improved imaging performance.

For the sake of completeness, it should be noted that not all annular zones 12 and not all areas of the surface of the lens body 14 have to be provided with a topographic relief structure 16, but the topographic relief structures 16 can also only be formed in some annular zones 12 according to some optional embodiments . It is also pointed out that the relief-like structures 16 can alternatively or additionally in principle also be formed inside the lens body 14 and/or on the lower surface of the lens body 14.

3 explains an ophthalmic lens 10 according to a further optional embodiment using two graphs. The course of the topographic relief structure 16 relative to the base surface 14a is plotted in the lower graph, ie the topographic profiles h ₀ to h ₃ etc. of the individual annular zones 12. The horizontal axis indicates the (linear) radius in millimeters and the vertical axis the sagittal differential height of the topographic relief structure in micrometers, ie the elevation or depression of the topographic relief structure relative to the regular surface 14a of the lens body 14. The first six annular zones 12 are identified, for example, with curly brackets and a corresponding line and with Z1 to Z6. Furthermore, the individual annular zones 12 are each divided into a main subzone 12a and a phase subzone 12b. The main subzones 12a take up the majority of the respective annular zone 12, while the phase subzones 12b only form the edge of the respective annular zone 12, in which the topographic relief structure 16 is returned to the base surface 14a according to the optional embodiment shown. As can be seen in the graph, all annular zones 12 have different widths and zone areas. It can also be seen that the relief heights of the individual topographic relief structures 16 in the individual annular zones 12 are different from one another. According to the embodiment shown, the topographical relief structures 16 only have recesses, so that the topographical relief structures 16 cause the surface of the ophthalmic lens 10 to curve, which lies below the base surface 14a.

The upper graph shows the phase shifts 18 resulting from the annular zones 12 and from the topographic relief structures 16 of the partial waves propagating through the respective annular zones 12, ie the phase profile 18 of the ophthalmic lens 10 and the individual annular zones 12. The graphs are for better comparison arranged in such a way that the (linear) radius in millimeters is plotted on the horizontal axis in the same way. The phase shift 18 is plotted in design wavelengths on the vertical axis, with the value 1.0 representing a whole wavelength of the design wavelength. It can be seen that the phase shifts 18 in the different annular zones 12, ie for the different partial waves, have different values from one another and are even different from one another in pairs. The phase shifts 18 in the first three annular zones Z1 to Z3 are identified by corresponding auxiliary lines δ ₁ to δ ₃ . While the phase shifts 18 build up radially outward in the main subzones 12a, these are returned to zero in the phase subzones 12b according to the embodiment shown. It can be seen that the maximum value of the individual phase shifts 18 is each less than one and the phase shift 18 is therefore less than one wavelength of the design wavelength. This enables a coherent superposition of the partial waves in the focal area of the ophthalmic lens 10.

4 shows in an exemplary graph the phase profile 18 of an ophthalmic lens 10 according to a further optional embodiment, with the square radius r ² of the ophthalmic lens 10 in mm ² being plotted on the horizontal axis. The phases are on the vertical axis shift plotted in design wavelengths. The linear course of the phase shifts 18 compared to the square radius reveals a complete or at least approximately parabolic course of the phase shifts 18 with the radius over the individual annular zones 12, with the phase shift 18 being returned to zero at the border between two annular zones 12. Both the different widths and zone areas of the annular zones Z1 to Z7 as well as the different maximum values of the phase shifts 18, of which the values δ ₁ to δ ₃ are exemplified, contribute to the avoidance of undesirable periodicities in the surface structure of the ophthalmic lens 10 and thus to Avoiding unwanted interference and artifacts. The different zone areas and maximum values of the phase shifts 18 also result in different slopes of the phase shifts 18 plotted against the square radius, which can also be viewed as an indicator of the measures to avoid periodicities in the surface structure of the ophthalmic lens 10. According to other optional embodiments, not all phase shifts 18 of the annular zones 12 have a parabolic course, but can, for example, also have a linear, hyperbolic and/or circular course.

5 shows a topographical surface profile and a phase profile 18 of an ophthalmic lens 10 according to a further optional embodiment. The graph in section a) shows the topographic surface profile in the form of the differential sagittal height in micrometers compared to the base surface 14a compared to the linear radius r in millimeters, section b) the phase profile 18 in design wavelengths compared to the linear radius r in millimeters, and section c ) the phase profile 18 versus the squared radius in mm ² .

As can be seen, among other things, in section c), the topographic profile and in particular all topographic relief structures 16 in the annular zones 16 Z1 to Z7 have a symmetrical course with respect to the base surface 14a depending on the square radius. In other words, the base surface 14a of the lens body 14 forms a common line of symmetry for the phase profile 18 and correspondingly for the diffraction profile. An advantage of this embodiment can be an improved diffraction efficiency in the desired refractive power ranges compared to the return to a common baseline or base curve. The base curve is a two-dimensional construct along a meridian of the surface.

6 shows the surface profile and the phase profile of a further optional embodiment of an ophthalmic lens 10, which differs from the previous embodiments in that the phase profile has neither a common line of symmetry (across all annular zones) nor a common baseline to which the phase profiles 18 in each annular zone 12. This can provide further advantages in avoiding periodicities and avoiding artifacts.

The graph in section a) shows the topographical surface profile in the form of the differential sagittal height in micrometers relative to the base surface 14a versus the linear radius r in millimeters, section b) the phase profile 18 in wave periods versus the linear radius r in millimeters, and section c ) the phase profile 18 versus the squared radius in mm ² . For better visibility, the respective starting points and end points of the topographic relief structures 16 in the first two annular zones Z1 and Z2 are identified in section a) with h _{1, start} and h _{1, end} or h _{2, start} and h _{2, end} . Likewise, in sections b) and c), the starting points and end points of the phase shifts 18 in the first two annular zones Z1 and Z2 are identified with δ _1,start and δ _1,end or δ _2,start and δ _2,end .

As can be seen in section a), the topographic relief structures 16 extend asymmetrically around the base surface 14a, with neither the beginning of the topographic relief structures nor the end of the topographic relief structures of the annular zones 12 (with the exception of the innermost annular zone Z1). the base surface 14 lies.

The following is with reference to 7 By way of example, a method 700 for designing an ophthalmic lens 10 according to an optional embodiment is explained, without the disclosure being limited to this example. The method 700 includes, in a first step 702, determining a subdivision of the ophthalmic lens 10 into a plurality of concentrically arranged annular zones 12. In addition, the method includes, in a step 704, determining topographic relief structures 16 for the annular zones 12 such that the annular zones 12 a phase shift 18 for one through the respective annular zone 12 cause partial wave propagating, the phase shifts 18 in the annular zones 12 being at least partially different from one another and each having one of at least five different predetermined values. Optionally, the method may include a further step 706 for producing the ophthalmic lens 10 according to the specified subdivision and according to the specified topographic relief structures 16 and thus represent a method for producing an ophthalmic lens 10.

The topographical relief structures 16 and/or the annular zones 12 can be determined on the basis of a random distribution. For example, the topographic relief structures 16 and/or the annular zones 12 can be determined within the framework of a computer-implemented method, such as by means of a Monte Carlo simulation. The random distribution can be based on a predetermined distribution of the annular zones 12 and/or the topographic relief structures 16 as a starting point. For example, a Fresnel division can serve as a starting point, in which all annular zones have the same zone areas.

• - absolute Maximalwerte der Phasenverschiebungen 18 (δ) in den jeweiligen annularen Zonen 12;
• - Start- und Endpunkte der Phasenverschiebungen 18 (δ_i,start; δ_i,end), wobei der Index i die jeweilige annulare Zone indiziert;
• - die maximale Höhe bzw. Relieftiefe der jeweiligen topographischen Reliefstrukturen 16, sowie deren jeweilige Anfangs- und End-Höhe (hi, h_i,start, h_i,end),

Determining the annular zones 12 and/or the topographic structures 16 can include optimizing the optical properties of the ophthalmic lens 10 by varying one or more randomizable parameters as part of the computer-implemented method. For example, the phase shifts 18 caused in the annular zones 12 by the respective topographic relief structures 16 can be varied. Possible randomizable parameters for the variation of the phase shifts 18 between the individual annular zones 12 can represent the following parameters:

• - absolute maximum values of the phase shifts 18 (δ) in the respective annular zones 12;
• - Start and end points of the phase shifts 18 (δ _i,start ; δ _i,end ), where the index i indicates the respective annular zone;
• - the maximum height or relief depth of the respective topographic relief structures 16, as well as their respective start and end heights (hi, h _{i, start} , h _{i, end} ),

Likewise, sizes of the ophthalmic lens equivalent to the parameters mentioned can be changed to achieve the same effect.

• - Variation der Breite der annularen Zonen 12, sodass diese in Abhängigkeit vom quadratischen Radius des ophthalmischen Linse 10 unterschiedliche Breiten aufweisen (dargestellt in den 5 und 6 als w_i, wobei i die Nummer der jeweiligen annularen Zone 12 indiziert);
• - Variation des Additionsbrechwerts P_add,i der einzelnen annularen Zonen 12;
• - Variation der Zonenfläche A_Zone,i der einzelnen annularen Zonen 12;

Alternatively or additionally, the following parameters relating to the annular zones 12 can be varied:

• - Variation of the width of the annular zones 12 so that they have different widths depending on the square radius of the ophthalmic lens 10 (shown in the 5 and 6 as w _i , where i indexes the number of the respective annular zone 12);
• - Variation of the addition power P _add,i of the individual annular zones 12;
• - Variation of the zone area A _Zone,i of the individual annular zones 12;

$${\text{P}}_{add}=\left(2\lambda \pi \right)/{\text{P}}_{add}$$

$${\text{n}}_{zones}=\left({\text{P}}_{add}{\text{ r}}_{max}{}^2\right)/\left(2\lambda \right)$$

The zone area A _Zone , the addition refractive index P _add and the number of zones n _zones are defined as follows and are interdependent: $${\text{A}}_{ZOne}=\left(2\lambda \pi \right)/P_{add}$$

$${\text{P}}_{add}=\left(2\lambda \pi \right)/{\text{P}}_{add}$$

$${\text{n}}_{\mathrm{e.g}Ones}=\left({\text{P}}_{add}{\text{r}}_{max}{}^2\right)/\left(2\lambda \right)$$

Where λ indicates the design wavelength and r _max indicates the maximum radius of the ophthalmic lens 10 provided with annular zones.

For example, a range of values in which the variation should take place can be specified for the variation of the respective parameters. The following table shows exemplary value ranges which can be suitable for the variation or randomization of the maximum value of the phase shifts 18 of the respective annular zones 12 and for the addition refractive index of the respective annular zones 12: Average Standard deviation (σ) Cutting the value range (τ) Maximum value of phase shift for annular zone (δ _i ) 0.3λ - 0.8λ 0.1λ - 0.6λ 1σ - 3σ (0.4λ - 0.6λ) (0.05λ - 0.2λ) (1σ - 2σ) Addition power per annular zone padd 0.8D - 2.8D 0.1D-1.0D 1σ - 3σ (1.0D-2.0D) (0.3D - 0.6D) (1σ - 2σ)

The value ranges specified in brackets are optional value ranges, which can be particularly advantageous.

For example, the method can produce a design for an ophthalmic lens 10 whose surface profile is designed such that the ophthalmic lens 10 has the following exemplary values: P _{add, zone, odd} (mean) = 1.4 D δ ₁ (mean) = 0.55λ σ (P _{add, Zone} ) = 0.46 D σ(δ ₁ ) = 0.25λ τ (P _{add, Zone} ) = 0.65 D τ(δ ₁ ) = 0.35λ

The standard deviation σ characterizes the standard deviation of the maximum values of the phase shifts in the annular zones 12 from the specified mean value. The cut of the value range is a predetermined value range of the predetermined distribution function, the values of which should be taken into account, while values lying outside this range should be ignored. This can serve to avoid values that are too small and/or too large, for example for the zone area, which could lead to a design that does not make technical sense and/or could not be technically feasible.

8A shows, by way of example, a predetermined distribution function 802 in graph 800, which corresponds to a predetermined normal distribution 804 with an applied cut 806 of the value range. The addition power in diopters is plotted on the horizontal axis. The bars 808 indicate by way of example the relative frequency of annular zones 12 with the respective addition power in an example of a design of an ophthalmic lens 10 resulting from the process. The vertical line 810 indicates the mean value.

8B shows an example of a predetermined distribution function 812, which corresponds to a predetermined normal distribution 814 with an applied cut 816 of the value range. The phase shift in wavelengths of the design wavelength is plotted on the horizontal axis. The bars 818 indicate by way of example the relative frequency of annular zones with the respective addition power in an example of a design of an ophthalmic lens 10 resulting from the process. The vertical line 820 indicates the mean value.

A method for creating a design for an ophthalmic lens can generate a variety of solutions for the optimization task and thus a variety of possible designs. The method can therefore optionally include, as a further method step, selecting one or more designs from the set of results. Selecting one or more designs can include specifying value ranges for one or more parameters of the designs, which can be used to assess whether the respective designs should be taken into account or not.

• - eine monochromatische Beugungseffizienz bei vorher festgelegten Defokuswerten, insbesondere in Form eines Mindestwerts (Berechnung z.B. nach Fiala und Pingitzer 2000);
• - polychromatische Beugungseffizienz bei vorher festgelegten Defokuswerten, insbesondere in Form eines Mindestwerts, (Berechnung z.B. nach Fiala und Pingitzer 2000);
• - Beugungseffizienz bei Defokus = 0 D, insbesondere in Form eines Mindestwerts (Berechnung z.B. nach Fiala und Pingitzer 2000);
• - Modulationstransferfunktion, (monochromatisch und/oder polychromatisch), bei vorher festgelegten Defokuswerten, insbesondere in Form eines Mindestwertes oder in Form einer Mindestkurve;
• - Homogenität der Defokuskurve;
• - Breite der Defokuskurve, insbesondere in Form eines Mindestwertes;
• - residuale Beugungseffizienz außerhalb des gewünschten Defokusbereiches (Minimierung zur Vermeidung von Halos und Dysphotopsien), insbesondere in Form eines Maximalwerts oder einer Maximalkurve.

For example, one of several of the following parameters can be used to select the designs from the set of results of a Monte Carlo simulation:

• - a monochromatic diffraction efficiency at predetermined defocus values, especially in the form of a minimum value (calculation, for example, according to Fiala and Pingitzer 2000);
• - polychromatic diffraction efficiency at predetermined defocus values, especially in the form of a minimum value (calculation, for example, according to Fiala and Pingitzer 2000);
• - Diffraction efficiency at defocus = 0 D, especially in the form of a minimum value (calculation e.g. according to Fiala and Pingitzer 2000);
• - modulation transfer function, (monochromatic and/or polychromatic), at predetermined defocus values, in particular in the form of a minimum value or in the form of a minimum curve;
• - Homogeneity of the defocus curve;
• - width of the defocus curve, especially in the form of a minimum value;
• - residual diffraction efficiency outside the desired defocus range (minimization to avoid halos and dysphotopsia), especially in the form of a maximum value or a maximum curve.

A defocus curve is understood to be a plot of an imaging power versus a deviation from the intended optical effect (in diopters). A defocus of zero corresponds to the intended optical effect.

• - eine monochromatische Beugungseffizienz bei vorher festgelegten Defokuswerten, Berechnung z.B. nach (Fiala und Pingitzer 2000);
• - eine polychromatische Beugungseffizienz bei vorher festgelegten Defokuswerten, Berechnung z.B. nach (Fiala und Pingitzer 2000);
• - eine Beugungseffizienz bei Defokus = 0 D, Berechnung z.B. nach (Fiala und Pingitzer 2000);
• - eine vorbestimme Ausgestaltung einer Modulationstransferfunktion (MTF) der berechneten Designs, allgemein oder insbesondere bei vorbestimmten Defokuswerten (monochromatisch oder polychromatisch), insbesondere in Form einer Mindestkurve und/oder eines Mindestwerts;
• - Homogenität einer Defokuskurve;
• - eine Breite der Defokuskurve;
• - eine residuale Beugungseffizienz außerhalb des gewünschten Defokusbereichs (Minimierung zur Vermeidung von Halos und Dysphotopsien).

To select possible designs for an ophthalmic lens from the list of results of a Monte Carlo simulation, one or more of the following parameters can alternatively or additionally be used:

• - a monochromatic diffraction efficiency at predetermined defocus values, calculated for example according to (Fiala and Pingitzer 2000);
• - a polychromatic diffraction efficiency at predetermined defocus values, calculated for example according to (Fiala and Pingitzer 2000);
• - a diffraction efficiency at defocus = 0 D, calculated for example according to (Fiala and Pingitzer 2000);
• - a predetermined configuration of a modulation transfer function (MTF) of the calculated designs, generally or in particular at predetermined defocus values (monochromatic or polychromatic), in particular in the form of a minimum curve and/or a minimum value;
• - Homogeneity of a defocus curve;
• - a width of the defocus curve;
• - a residual diffraction efficiency outside the desired defocus range (minimization to avoid halos and dysphotopsia).

• Fiala, W.; Pingitzer, J. (2000): Analytical approach to diffractive multifocal lenses. In: Eur. Phys. J. AP 9 (3), S. 227-234 .

“Fiala and Pingitzer 2000” refers to the following publication:

• Fiala, W.; Pingitzer, J. (2000): Analytical approach to diffractive multifocal lenses. In: Eur. Phys. J. AP 9 (3), pp. 227-234 .

Alternatively or in addition to the above-mentioned parameters, further parameters relevant to the imaging quality and/or manufacturability of an ophthalmic lens 10 can be used for selection.

The listed parameters can be analyzed and evaluated for a fixed pupil size or optionally for several different pupil sizes.

In particular, combined selection criteria can optionally be used to select the designs. These can include, for example, the imaging performance at different pupil sizes.

9 shows an example of a series of possible target functions for the relative imaging performance of a target design in a given defocus range from -1.0 D to 2.5 D (horizontal axis) for different pupil diameters. These can be used as the basis for a selection. For example, the target functions can be specified together with a permissible standard deviation and/or squared deviation, so that only those designs should be selected from the set of solutions whose imaging performance for the specified pupil diameters is within the specified deviation from the respective target function. In 9 graphs 900, 902, 906 and 908 show the imaging powers for pupil diameters of 1.5 mm, 1.75 mm, 2.0 mm and 2.25 mm, respectively. Ent Speaking of this, a selection of the pupil diameters that should be taken into account during the selection can also be used as a selection criterion.

• - Intensitäten und/oder Beugungseffizienzen bei mehreren Defokuszuständen;
• - Intensitäten und/oder Beugungseffizienz bei Defokus = 0,0 D und Fläche unter der Defokuskurve;
• - Intensität und/oder Beugungseffizienz bei Defokus = 0,0 D und Breite der Defokuskurve;
• - Intensität und/oder Beugungseffizienz bei Defokus = 0,0 D und Breite der Defokuskurve und Homogenität der Defokuskurve;

In addition, the selection criteria can optionally take into account one or more of the following exemplary parameters:

• - Intensities and/or diffraction efficiencies at multiple defocus states;
• - Intensities and/or diffraction efficiency at defocus = 0.0 D and area under the defocus curve;
• - Intensity and/or diffraction efficiency at defocus = 0.0 D and width of the defocus curve;
• - Intensity and/or diffraction efficiency at defocus = 0.0 D and width of the defocus curve and homogeneity of the defocus curve;

Alternatively or additionally, a required radius for the topographic relief structures according to the designs generated can also be taken into account in the selection together with a minimum value and/or a maximum value.

• Belsley, David A.: Generating Random Numbers in Mathematica 6, S. 71-77. DOI: 10.10071978-1-4757-2644-2_5

The examples shown and mentioned in the present disclosure were calculated using the random number generator from WOLFRAM MATHEMATICA (version 13.0.1). This has an extremely long periodicity and other advantageous properties for generating random numbers according to certain distributions, as described in the following publication:

• Belsley, David A.: Generating Random Numbers in Mathematica 6, pp. 71-77. DOI: 10.10071978-1-4757-2644-2_5

The exemplary embodiments use randomly distributed numbers that obey a normal distribution tailored on both sides. The cut of the normal distribution is advantageous in order to exclude values that do not make physical sense. Otherwise, for example, a very small addition power could lead to a large zone area, which could exceed the lens radius of the ophthalmic lens 10. $$\begin{array}{l}\text{DesiredDistribution}\left[\text{xmin},\text{xmax},\mathrm{\mu },\mathrm{\sigma }\right]=\hfill \\ \text{TruncatedDistribution}\left[\left\{\text{xmin},\text{xmax}\right\},\text{NormalDistribution}\left[\mathrm{\mu },\mathrm{\sigma }\right]\right]\hfill \end{array}$$

TruncatedDistribution[ ] represents the distribution obtained by truncating the values of dis between xmin and xmax.

NormalDistribution[ ] represents a normal distribution (Gaussian curve) with mean µ and standard deviation σ.

DesiredDistribution[ ] represents the combination of both functions, with TruncatedDistribution[ ] applied to the NormalDistribution[ ].

Reference symbol list

10

ophthalmic lens

12

annular zone

12a

Main subzone

12b

phase subzone

14

Lens body

14a

Base surface of the lens body

16

topographic relief structure

18

Phase shift

700

Method for designing an ophthalmic lens

702 - 706

Procedural steps

800

graph

802, 812

resulting distribution function

804, 814

underlying distribution function

806, 816

Cropping the value range

808, 818

Frequency of values

810,820

Average

900 - 908

Target curves for imaging performance at different pupil sizes

1000

optical axis of the ophthalmic lens

Z1 - Z6

annular zones

h0...h3

topographic profile of the annular zones

δi

Maximum value of the phase shift in the ith annular zone

wi

Width of the ith annular zone when the radius is plotted squarely

QUOTES INCLUDED IN THE DESCRIPTION

This list of documents listed by the applicant was generated automatically and is included solely for the better information of the reader. The list is not part of the German patent or utility model application. The DPMA assumes no liability for any errors or omissions.

Cited patent literature

• EP 1194797 B1 [0003, 0025]
• EP 2377493 B1 [0003]

Non-patent literature cited

• Belsley, David A.: Generating Random Numbers in Mathematica 6, pp. 71-77 [0032]
• Fiala, W.; Pingitzer, J. (2000): Analytical approach to diffractive multifocal lenses. In: Eur. Phys. J. AP 9 (3), pp. 227-234 [0070]

Claims (20)

Ophthalmic lens (10) with an extended focus range, the ophthalmic lens (10) comprising a lens body (14) which has a plurality of concentrically arranged annular zones (12), wherein: - each of the annular zones (12) has a predetermined design power which is different from the respective design power of the immediately adjacent annular zones (12); and - Each of the annular zones (12) has a topographic relief structure (16), which is designed to cause a phase shift (18) for a partial wave propagating through the respective annular zone (12), the phase shifts (18) being in the annular zones (12) at least partially differ from each other and each have one of at least five different predetermined values. Ophthalmic lens (10) according to Claim 1 , whereby the phase shifts (18) in the annular zones (12) caused by the topographic relief structures (16) are not more than twice a design wavelength. Ophthalmic lens (10) according to Claim 1 or 2 , whereby the phase shifts (18) in the annular zones (12) caused by the topographic relief structures (16) are different from one another in pairs. Ophthalmic lens (10) according to one of the preceding claims, wherein each of the annular zones (12) has a predetermined zone area and wherein the predetermined zone areas of the annular zones (12) are at least partially different from one another. Ophthalmic lens (10) according to Claim 4 , wherein the annular zones (12) each have one of at least two different predetermined zone areas and optionally one of at least five different predetermined zone areas. Ophthalmic lens (10) according to Claim 4 or 5 , wherein the predetermined zone areas of the plurality of annular zones (12) are different from one another in pairs. Ophthalmic lens (10) according to one of the preceding claims, wherein ophthalmic lens (10) has a number of at least 10 annular zones (12) and optionally at least 20 annular zones (12) and optionally not more than 60 annular zones (12) and optionally has no more than 50 annular zones (12). Ophthalmic lens (10) according to one of the preceding claims, wherein at least one of the plurality of annular zones (12) and optionally all of the plurality of annular zones (12) each have a main sub-zone (12a) and a phase sub-zone (12b). Ophthalmic lens (10) according to one of the preceding claims, wherein the respective topographic relief structures (16) of the annular zones (12) differ at least partially in their relief depth. Ophthalmic lens (10) according to Claim 9 , wherein the topographic relief structures (16) of the annular zones (12) each have one of at least two different predetermined relief depths and optionally one of at least five different predetermined relief depths. Ophthalmic lens (10) according to Claim 9 or 10 , wherein the predetermined relief depths of the topographic relief structures (16) of the several annular zones (12) are different from one another in pairs. An ophthalmic lens (10) according to any one of the preceding claims, wherein the predetermined zone areas of the plurality of annular zones (12) are each in a range of 0.3 mm ² and 2 mm ² . Ophthalmic lens (10) according to one of the preceding claims, wherein the ophthalmic lens (10) is designed as an intraocular lens. Method for designing an ophthalmic lens (10), the method comprising: - determining a subdivision of the ophthalmic lens (10) into several concentrically arranged annu lare zones (12); - Determining topographic relief structures (16) for the annular zones (12) in such a way that the annular zones (12) cause a phase shift (18) for a partial wave propagating through the respective annular zone (12), the phase shifts (18) in the annular zones (12) at least partially differ from each other and each have one of at least five different predetermined values. Procedure according to Claim 14 , wherein the topographical relief structures (16) are determined in such a way that the phase shifts (18) of the several annular zones (12) caused by the topographical relief structures (16) are different in pairs. Procedure according to Claim 14 or 15 , whereby the topographic relief structures (16) and/or the annular zones are determined on the basis of a random distribution. Procedure according to one of the Claims 14 until 15 , wherein determining the topographic relief structures (16) includes varying the respective zone areas of the annular zones (12) based on predetermined initial values for the respective zone areas and/or varying the respective relief depths based on predetermined initial values for the respective relief depths. Procedure according to Claim 17 , wherein the predetermined initial values for the respective zone areas and / or relief depths are predetermined such that the initial values for the respective zone areas and / or respective relief depths correspond to a Fresnel division. Method for producing an ophthalmic lens (10), the method comprising: - Determining a subdivision of the ophthalmic lens (10) into several concentrically arranged annular zones (12); - Determining topographic relief structures (16) for the annular zones (12) in such a way that the annular zones (12) cause a phase shift (18) for a partial wave propagating through the respective annular zone (12), the phase shifts (18) in the annular zones (12) at least partially differ from one another and each have one of at least five different predetermined values; - Manufacture the ophthalmic lens (10) according to the specified subdivision and according to the specified topographic relief structures (16). Use of a division into several annular zones (12) with at least partially different zone areas and/or with topographic relief structures (16) with at least partially different relief depths to expand a focal area of an ophthalmic lens (10).

Images