Device for inspecting vision through intraocular lens

Abstract

The invention relates to a device (16) for checking vision through an intraocular lens (8), comprising a carrier (17) which, in succession on a central vision axis (5) from the distal end to the proximal end, supports a corneal optical device (18), a holding device (19) for the intraocular lens (8) and an eyepiece optical device (20), wherein the eyepiece optical device (20) comprises a correction lens (23) at a distal end and a diverging lens (24) and a converging lens (25) at a proximal end relative to the distal end, and wherein the correction lens (23) has a distal concave lens surface (26) and a proximal convex lens surface (27).

Description

Technical Field

[0001] The invention relates to a device for checking vision through an intraocular lens, which has a carrier which successively supports corneal optics, a holding device for the intraocular lens and eyepiece optics on a central visual axis from distal to proximal. Background Art

[0002] The implantation of a phakic, aphakic or pseudophakic intraocular lens (IOL) into the patient's eye is a critical process. The IOL must be adapted as closely as possible to the individual requirements of the patient, since every subsequent replacement would entail unnecessary surgical risks. It is therefore necessary and desirable to thoroughly check the patient's field of vision through the IOL to be implanted or its optical properties before the implantation, in order to avoid in vivo replacements under any circumstances.

[0003] Conventionally, this is done either by computer simulations or by optical examination devices in which the IOL to be implanted is used. However, the images displayed to the patient, which are created by means of computer simulations of an eye with an average anatomical structure, always reflect only very general properties of the IOL. It is therefore not possible to reliably predict the patient's subjective visual impression through the IOL selected for implantation with the aid of simulations. Furthermore, it is particularly difficult to reliably simulate different visual situations, such as different lighting conditions and visibility, such as farsightedness when viewing a landscape and nearsightedness when reading a book.

[0004] Optical examination devices are better suited for examining subjective visual impressions in different situations. However, currently known examination devices are severely limited in their field of view, so that a wide range of viewing angles of the patient cannot be examined.

[0005] Figures 1 to 3 Such a conventional optical examination device 1 is shown, which has a carrier 2, which supports a corneal optical device 6 (also called corneal model optical device), a holding device 7 for an IOL 8 and a converging lens 9 along a central visual axis 5 from the distal end (close to the observed environment 3) to the proximal end (close to the patient's eye 4). If the visual axis 5' ( Figure 2 ), the light beam 10 ′ passing through the device 1 —and thus the perceptible image—is increasingly clipped by the iris 11 of the eye 4 ( Figure 3 ). Moreover, due to the defocus, the actually perceived residual image has a contrast and resolution that is significantly different from the contrast and resolution of the IOL 8 in the actually implanted state, hereinafter referred to as the "implanted IOL", as seen from the device 1 in the Figure 4 As can be seen from the modulation transfer function (MTF) shown in FIG. 1 , on the one hand for viewing angles α=0° (dotted line 12 ), α=2.5° (dashed line 13 ) and α=5° (dotted line 14 ) and on the other hand for the expected MTF of the implanted IOL 8 (solid line 15 ).

[0006] For all the reasons stated, it is always difficult for the patient to select an IOL that ensures the optimal subjective visual impression from the various embodiments of IOLs, whether they are monofocal lenses, bifocal lenses, multifocal lenses, EDOF (“Extended Depth of Focus”) lenses, light-adjustable lenses (LAL), etc. Summary of the invention

[0007] The present invention has as its object to achieve a device for checking vision through an IOL which overcomes the disadvantages of the prior art and enables a lens inspection with an extended field of view.

[0008] This object is achieved by means of a device of the type mentioned at the outset, which is characterized according to the invention in that the eyepiece optical device comprises a correction lens at the distal end and a diverging lens and a converging lens at the proximal end relative to the distal end, wherein the correction lens has a concave lens surface at the distal end and a convex lens surface at the proximal end.

[0009] The combination of a correcting lens, a diverging lens and a converging lens in the eyepiece optical device according to the invention allows, by means of a specific shape of the lens surfaces, to extend the field of view of the device or of the patient's eye observing through the device, and at the same time to correct and preferably eliminate defocus and contrast errors in the extended field of view.

[0010] Thus, by the interaction of the concave-convex correction lens according to the invention and the downstream diverging and converging lenses, for different angles of incidence of the light beam, different vergence and different angular differences between the respective incident and exiting light beams with respect to the central visual axis or optical axis are generated. Said specific vergence and angular differences allow precisely - in combination with the corneal optics - for different viewing angles to deflect the light beams incident from the respective spatial angles to substantially the same point of the eye, so that a viewing angle correction is obtained, i.e. a line of sight that is consistent with the implanted IOL in terms of resolution and contrast is obtained by the IOL for different viewing angles.

[0011] The corneal optical device can here - in a particularly effective variant - model an average cornea, for example according to the Liou-Brennan eye model, in order to carry out a quick visual examination; or - in a particularly precise variant - model the cornea of ​​the individual patient, for example after a previous measurement thereof, in order to enable the most realistic possible examination of the IOL for the individual patient.

[0012] In particular, the device according to the invention enables the subjective visual impression through the IOL to be checked in different situations, whether for hyperopia or myopia. The device according to the invention is therefore particularly suitable for checking a variety of intraocular lenses, such as monofocal lenses, bifocal lenses, multifocal lenses or EDOF lenses. In order to quickly check a plurality of different intraocular lenses, the holding device can be embodied as an exchangeable glass vessel, in which the IOL is arranged.

[0013] In summary, with the aid of the device according to the invention, a realistic subjective visual impression can be provided to the patient over a larger visual field already before the implantation of the IOL - as if the IOL had already been implanted - and the selection of a suitable IOL is facilitated.

[0014] In a preferred embodiment, at least one of the lens surfaces of the diverging lens and the converging lens facing each other is aspherical. This allows, in interaction with the concave-convex correction lens and the corneal optics, a particularly good viewing angle correction, i.e. a particularly well-focused line of sight through the IOL that corresponds to the implanted IOL in terms of resolution and contrast for different viewing angles, to be achieved.

[0015] In an advantageous embodiment, at least one of the lens surfaces of the diverging lens and the converging lens that face each other is an aspheric surface of at least the fourth order. The use of such an aspheric lens allows to avoid or correct imaging errors such as spherical aberration, astigmatism, etc. Thus, an error-free observation through the IOL can be achieved for the patient over a wide field of view, thereby enabling an accurate inspection of the IOL. Although the use of higher-order aspheric surfaces provides great flexibility in the design of the eyepiece optical device, low-order aspheric surfaces can be manufactured more simply and their influence on the optical path can be predicted more simply.

[0016] In a particularly advantageous variant, the fourth-order asphere and the height of the arrow measured at the vertex plane away from the asphere are selected as follows:

[0017] Where A4<0, (1)

[0018] in

[0019] z1 is the height of the arrow measured from the distal end to the proximal end,

[0020] ρ vertex curvature,

[0021] r is the radial distance from the central visual axis, and

[0022] A2 and A4 are preset coefficients, wherein when the aspherical surface is the lens surface of a converging lens, A2>0, and when the aspherical surface is the lens surface of a diverging lens, A2<0.

[0023] Such a lens surface, whose arrow height follows a low-order continuous function, can be manufactured simply and accurately.

[0024] If the aspheric surface is the lens surface at the distal end of the converging lens, this can facilitate manufacturing and further improve the achievable viewing angle correction of the device.

[0025] In order to simplify the production of the aspheric surface in particular, it is advantageous if the lens surface of the converging or diverging lens opposite the aspheric surface is flat. For this purpose, the converging or diverging lens can optionally consist of a plurality of individual lenses spaced apart from one another.

[0026] In an advantageous variant, at least one of the corneal optics and the eyepiece optics has an achromat or apochromat in order to avoid chromatic aberrations. This allows lens inspections to be performed for a large field of view that are consistent with the implanted IOL in terms of resolution, focus and contrast for multiple wavelengths. In addition, spherical aberrations can be avoided or corrected by means of an achromat or apochromat. For example, in this variant, a dispersion-free and angle-of-incidence collimation of the light beam passing through the device can be achieved in front of the patient's eye.

[0027] The corneal optical system can be designed in different ways. In one variant which is particularly simple in terms of production technology, the corneal optical system has a corneal diverging lens and a corneal converging lens which can be arranged in any order along the optical vision axis.

[0028] If the converging lens and the diverging lens of the corneal optics and / or the converging lens and the diverging lens of the eyepiece optics have different Abbe numbers, the corresponding converging lens and the diverging lens form an achromatic lens or an apochromatic lens, so that in addition to spherical aberration, chromatic aberration can also be corrected or eliminated. This makes it possible to carry out a particularly precise examination of the IOL for the patient and to judge the quality of the IOL not only in terms of sharpness but also in terms of color perception before its implantation, so that a suitable IOL can be found.

[0029] Tests have shown that it is advantageous if the distal lens surface of the corneal converging lens is an aspheric surface of at least the fourth order. Thus, in interaction with at least one aspheric surface of the eyepiece optics and the correction lens, a perspective-corrected lens examination can be achieved, for example, for viewing angles of more than 10°, thereby enabling a particularly realistic lens examination over a wide field of view for the patient.

[0030] It is particularly advantageous here if the arrow height of the distal lens surface measured from the vertex plane of the distal lens surface facing away from the corneal converging lens is selected as follows:

[0031] Where A2>0 and A4<0, (2) where

[0032] z2 is the height of the arrow measured from the far end to the near end,

[0033] ρ vertex curvature,

[0034] r the radial distance from the central visual axis, and

[0035] A2, A4 preset coefficients.

[0036] Such a distal lens surface, whose arrow height follows a low-order continuous function, can be manufactured simply and accurately.

[0037] The correction lens of the eyepiece optics can also be implemented in different ways. In a preferred embodiment, the distal and proximal lens surfaces of the correction lens are spherical, and the radius of curvature of the distal lens surface of the correction lens is numerically smaller than the radius of curvature of the proximal lens surface of the correction lens. With the aid of the correction lens, in interaction with the upstream corneal optics and the downstream diverging and converging lenses of the eyepiece optics, a strongly extended field of view can be achieved while avoiding defocusing and contrast errors in the extended field of view.

[0038] In all embodiments, it is advantageous if at least one of the elements: corneal optics, retaining device and eyepiece optics is mounted adjustably on a carrier along a central visual axis. Each of the elements mentioned can be adjusted either as a whole or, if one of the elements has sub-elements, such as the correction lens, convergence lens and divergence lens mentioned for the eyepiece optics, the sub-elements can also be adjusted individually. The adjustable mounting enables a rapid adaptation of the device to the patient's eye at the time of the visual examination, for example, a shift of the optical main plane of the optical device. As a result, the vergence of the light beam emerging from the eyepiece optics at the proximal end can be adapted to the patient's visual defects, for example, in order to correct spherical refractive errors. By means of the adaptation, even for patients with visual defects, a lens examination can be ensured which simulates the IOL in the implanted state with respect to contrast, resolution and focus.

[0039] It is also advantageous if at least one of the elements: corneal optics, holding device and eyepiece optics is mounted on the carrier so as to be adjustably disposed transversely to the central visual axis, in order to allow simple adjustment and alignment of the device.

[0040] It is particularly advantageous if the holding device is designed to receive an intraocular lens in an exchangeable manner. Such a quick-change holding device allows an already examined IOL to be replaced by a new IOL to be examined in the device within a short time. The quick exchange allows a plurality of different IOLs to be examined efficiently for a patient, so that the most suitable IOL for the patient can be selected for subsequent implantation based on the subjective visual impression.

[0041] In another aspect of the invention, there is provided a use of an eyepiece optical device in an apparatus for examining vision through an intraocular lens, the eyepiece optical device comprising a correction lens at a distal end and a diverging lens and a converging lens at a proximal end relative to the distal end, wherein the correction lens has a concave lens surface at the distal end and a convex lens surface at the proximal end, and wherein at least one of the lens surfaces of the diverging lens and the converging lens facing each other is preferably aspherical. With regard to the advantages and possible design solutions of the use of the eyepiece optical device in an optical examination apparatus, reference is made to the above embodiments of the apparatus according to the invention. BRIEF DESCRIPTION OF THE DRAWINGS

[0042] The present invention will be described in detail below based on the embodiments shown in the accompanying drawings. In the accompanying drawings:

[0043] Figure 1 shows in a schematic side view a device according to the prior art for checking vision through an intraocular lens together with an exemplary beam path of an eye for viewing the intraocular lens in the central visual axis;

[0044] Figure 2 Shown in a schematic side view Figure 1 A device together with an exemplary optical path for viewing an eye with an intraocular lens at a certain viewing angle;

[0045] Figure 3 Shown in a schematic side view Figure 2 eyes and in Figure 2 a light path that is defocused in the light path of the eye and clipped by the iris of the eye;

[0046] Figure 4 The comparison line chart shows that Figure 1 and Figure 2 Exemplary modulation transfer functions achieved by the device for different viewing angles;

[0047] Figure 5 A schematic side view shows a device according to the invention for checking vision through an intraocular lens together with an exemplary beam path of an eye for viewing the intraocular lens in the central visual axis;

[0048] Figure 6 Shown in a schematic side view Figure 5 A device together with an exemplary optical path for viewing an eye with an intraocular lens at a certain viewing angle;

[0049] Figure 7 Shown in a schematic side view Figure 6 eyes and in Figure 6 a light path that is focused in the light path of the eye and is not clipped by the iris of the eye;

[0050] Figure 8 The comparison line chart shows that Figure 5 and Figure 6 Exemplary modulation transfer functions achieved by the device for different viewing angles;

[0051] Fig. 9 Shown in exploded side view Figure 5 and Figure 6 The eyepiece optics of the device;

[0052] Fig.10 Shown in exploded side view Figure 5 and Figure 6 The corneal optics of the device;

[0053] Fig.11 The longitudinal chromatic aberration is shown in a graph with respect to wavelength. Figures 1 to 3 in the device and in Figures 5 to 7 illustrative color differences that occur in devices; and

[0054] Fig.12 The Zernike coefficients are plotted against the viewing angle as shown in Figures 1 to 3in a device or Figures 5 to 7 Example spherical aberration occurring in a device. DETAILED DESCRIPTION

[0055] according to Figures 1 to 4 A conventional optical inspection device 1 for an intraocular lens (IOL) 8 has been described above, as is known in the prior art. Figures 5 to 12 In the drawings, the same reference numerals denote the same Figures 1 to 4 The same parts in.

[0056] Figures 5 to 7 An optical inspection device 16 according to the invention is shown, which is used to inspect vision through an IOL 8 before it is implanted in a patient's eye 4. The IOL 8 to be inspected (which after its implantation - hereinafter referred to as "implanted IOL" - should lead to an improvement in the patient's vision) can be, for example, a monofocal lens, a bifocal lens, a multifocal lens, an EDOF (English "Extended Depth of Focus") lens, a light-adjustable lens (LAL), etc.

[0057] In order for the patient to obtain a subjective visual impression of the near, intermediate or far environment 3 through the not yet implanted IOL 8, the device 16 comprises a carrier 17, which carries a corneal optical device 18, a holding device 19 for the IOL 8 and an eyepiece optical device 20 successively along the central visual axis 5 from the distal end (close to the observed environment 3) to the proximal end (close to the patient's eye 4). To this end, the carrier 17 can be any device known in optical devices for supporting optical elements, such as a frame, a housing, a tube, an optical stand, an optical table, etc. The carrier 17 can support the optical elements either in a fixed position or adjustably. For example, the corneal optical device 18 (or its parts), the holding device 19 (or its parts) and / or the eyepiece optical device 20 (or its parts) can be displaced along the central visual axis 5 and / or can be adjustably supported orthogonal to the central visual axis at the carrier 17 in order to adjust them relative to each other.

[0058] The optical effect of the device 16 shall be described below in the case of a straight perspective along the central visual axis 5 ( Figure 5 ) and in the case of an oblique perspective along the visual axis 5' inclined at a viewing angle α ( Figure 6 ) According to two representative beams 10 ( Figure 5 ) or 10'( Figure 6 ) are described.

[0059] First, the light beam 10 or 10 ' incident from the environment 3, i.e. from the distal end of the device 16, passes through the cornea optical device 18 which optically simulates the cornea, in the example shown, through the distal cornea diverging lens 21 and the proximal cornea converging lens 22. In a first variant, the cornea optical device 18 forms the cornea of ​​an "average patient", for example, according to an eye model, such as, for example, the Liou-Brennan eye model. In an alternative variant, the cornea optical device 18 simulates the cornea of ​​an individualized patient's eye 4, for which purpose the cornea has been measured in advance, for example, optically or by means of ultrasound.

[0060] Downstream of the corneal optics 18 , the light beam 10 or 10 ′ is guided through the IOL 8 in a holding device 19 , which there—just as it would have been implanted in the eye 4 —focuses the light beam 10 or 10 ′ according to its refractive power.

[0061] The holding device 19 can be any holding device suitable for accommodating the IOL 8, such as a modular quick-change system having a first part fixedly supported at the carrier 17, the first part being used to accommodate a quickly exchangeable second part, the IOL 8 being accommodated in or at the second part so that different IOLs can be quickly checked by replacing the second part. For example, the holding device 19 can have a clamping holding device, a plug-in holding device or a magnetic holding device as a first part, the clamping holding device, the plug-in holding device or the magnetic holding device accommodating a replaceable glass vessel for the IOL as a second part, the glass vessel optionally being filled with a solution for simulating the inside of the eye.

[0062] Subsequently, the light beam 10 or 10 ′ passes through an eyepiece optical device 20, which comprises a correction lens 23 at the distal end and, at the proximal end relative to the distal end, a diverging lens 24 and a converging lens 25. As an alternative to the embodiment shown, the converging lens 25 can be arranged distally relative to the diverging lens 24. The correction lens 23 has a concave lens surface 26 at the distal end and a convex lens surface 27 at the proximal end, see Fig. 9 Optionally, at least one or both of the lens surfaces 28 , 29 of the diverging and converging lenses 24 , 25 facing each other are aspherical (here: the lens surface 29 at the distal end of the converging lens 25 ).

[0063] By means of the specific correction lens, diverging lens and converging lens 23-25, the light beam 10 or 10' is changed in vergence and direction in the eyepiece optical device 20 according to the viewing angle α, so that the light beam not only moves in a straight visual axis ( Figure 5 : α = 0°) and in the tilted visual axis ( Figure 6 and Figure 7 : α≠0°) is not clipped by the iris 11 of the eye 4. Of course, with a fixed viewing angle α, the light beam will not be clipped by the iris 11 even if it is incident at a slightly different angle, so that the light beam is also focused on a point on the periphery of the retina of the eye 4.

[0064] As from Figure 3 and Figure 7 As can be seen from the comparison of the apparatus 16 and the optical device 16, through the interaction of the correcting lens, the diverging lens and the converging lens 23-25 ​​of the eyepiece optical device 20, the light beam 10' propagating along the tilted visual axis 5' is no longer clipped by the iris 11 of the eye 4 in the apparatus 16 and is correctly focused on the retina of the eye 4. Therefore, the image perceived at a viewing angle α>0° is not only unclipped, but also better corresponds to the image of the conventional apparatus 1 in terms of contrast and resolution with the implanted IOL 8, as shown by the Figure 4 The modulation transfer function of the device 1 shown in Figure 8 A comparison of the modulation transfer functions of the device 16 shown in FIG. 1 shows in the diagram of contrast K over line pairs L that for α=0° (dash-dotted line 30), α=2.5° (dashed line 31) and α=5° (dotted line 32) there is respectively the expected MTF (solid line 15) of the implanted IOL 8. Thus, a larger field of view of the IOL 8 can be examined in the device 16 according to the invention than with the conventional device 1.

[0065] In the eyepiece optical device 20 Figure 5 , Figure 6 and Fig. 9 In the embodiment shown in FIG. 1 , at least one aspheric surface of the diverging and converging lenses 24, 25 is formed by the distal lens surface 29 of the converging lens 25. The aspheric surface can be generally described according to DIN ISO 10110 as follows: The arrow height z measured through the vertex plane away from the lens surface is described according to the radial spacing r from the central visual axis 5:

[0066]

[0067] in

[0068] ρ vertex curvature,

[0069] k the cone constant, and

[0070] A i Preset coefficients.

[0071] In a variant of the aspheric distal lens surface 29, the lens surface is an aspheric surface of at least fourth order, ie in equation (3), at least one coefficient A iis not equal to zero, where i≥4, where the first summand may be either present or absent. In an exemplary sub-variant thereof, the arrow height z1 of the distal lens surface 29 measured away from the vertex plane 33 of the distal lens surface 29 is selected as follows:

[0072] Where A2>0 and A4<0, (1)

[0073] z1 is the arrow height of the lens surface 29 at the distal end measured from the distal end to the proximal end,

[0074] ρ vertex curvature,

[0075] r is the radial distance from the central visual axis 5, and

[0076] A2, A4 preset coefficients.

[0077] In an alternative variant of the eyepiece optics 20, the aspheric surface of which is formed by the proximal lens surface 28 of the diverging lens 24, the lens surface 28 is an aspheric surface of at least fourth order, and in an exemplary sub-variant thereof, the arrow height of the distal lens surface measured away from the vertex plane of the proximal lens surface 28 is selected as follows:

[0078] Where A2<0 and A4<0, (1') where

[0079] z 1’ The arrow height of the lens surface 28 at the proximal end is measured from the distal end to the proximal end,

[0080] ρ vertex curvature,

[0081] r is the radial distance from the central visual axis 5, and

[0082] A2, A4 preset coefficients.

[0083] In the embodiment shown, the diverging lens 24 is optionally flat-concave and the converging lens 25 is formed by a convex-flat first section 251 and a flat-convex second section 252. As a result, the lens surface 34 opposite the aspherical lens surface 29 is flat and the aspherical surface can be manufactured more simply. In addition, the light beam 10 or 10 ′ is directed to the eye 4 in a collimated manner by the curvature of the proximal lens surface (here: the proximal lens surface 35 of the proximal section 252).

[0084] In another alternative embodiment, the diverging lens 24 and the converging lens 25 may have different Abbe numbers so as to form an achromatic lens.

[0085] For the purpose of increasing the viewing angle, the concave-convex correction lens 23 can be designed in many ways, for example, its distal and proximal lens surfaces 26, 27 themselves can be spherical or aspherical, respectively. Fig. 9 In the variant shown in , the two lens surfaces 26, 27 of the correction lens 23 are spherical. In addition, the distal lens surface 26 is more strongly curved than the proximal lens surface 27, that is, the radius of curvature of the former is smaller in value than the radius of curvature of the latter.

[0086] Corneal optical device 18 can also be designed in many ways. Figure 5 , Figure 6 and Fig.10 In the embodiment shown in the figure, the corneal optical device 18 is formed by a (here: concave-flat) corneal diverging lens 21 and a (here: convex-flat) corneal converging lens 22, which can be arranged either in the shown order with a distal corneal diverging lens and a proximal corneal converging lens 21, 22, or in the opposite order with a distal corneal converging lens and a proximal corneal diverging lens 21, 22.

[0087] In a variant thereof, the corneal diverging lens 21 and the corneal converging lens 22 have different Abbe numbers, forming an achromatic lens which optionally corrects chromatic aberrations in addition to spherical aberrations.

[0088] Furthermore, in the illustrated embodiment, the distal lens surface 36 of the corneal convergence lens 22 is an aspheric surface. In a variant, the aspheric surface is a fourth-order aspheric surface, and in an exemplary sub-variant thereof, the arrow height z2 of the distal lens surface 36 measured away from the vertex plane 37 of the distal lens surface 36 is selected as follows:

[0089] Where A2>0 and A4<0, (2) where

[0090] z2 is the height of the arrow measured from the far end to the near end,

[0091] ρ vertex curvature,

[0092] r is the radial distance from the central visual axis 5, and

[0093] A2, A4 preset coefficients.

[0094] Alternatively or alternatively thereto, the corneal diverging lens 21 can have an aspherical lens surface.

[0095] Of course, other designs of the corneal optical device 18 and / or the eyepiece optical device 20 with additional or other optical elements are also feasible, such as having an achromatic lens or apochromatic lens for color correction and / or a proximal lens for focusing or defocusing, a mirror for light beam deflection, etc.

[0096] Furthermore, it should be noted that each of the lenses 21 - 25 can be embodied not only in one piece but also in a plurality of—optionally separate from one another—segments, as is shown here in the case of lens 25 .

[0097] In the experiment, with a vertex curvature ρ between 0.058 / mm and 0.118 / mm, preferably 0.088 / mm, at 1·10 -5 / mm and 4.4·10 -5 / mm, preferably 2.7·10 -5 / mm coefficient A2, at -0.6·10 -4 / mm 3 and -1.6·10 -4 / mm 3 Between, preferably -1.1·10 -4 / mm 3 The aspherical lens surface 36 of the corneal convergence lens 22 has a coefficient A4; and by having a vertex curvature ρ between 0.01 / mm and 0.09 / mm, preferably 0.05 / mm, a coefficient A2 between 0.005 / mm and 0.025 / mm, preferably 0.015 / mm, a curvature of -1·10 -5 / mm 3 and-9·10 -5 / mm 3 Between, preferably -5·10 -5 / mm 3 A particularly good field of view expansion is achieved by means of an aspherical lens surface 29 of a converging lens 25 with a coefficient A4; and a correction lens 23 with a distal lens surface 26 having a spherical surface with a radius of curvature between -18 mm and -7 mm, preferably -12.5 mm, and a proximal lens surface 27 with a spherical surface with a radius of curvature between -19 mm and -7 mm, preferably -13 mm.

[0098] Fig.11 and Fig.12 The diagram shows the results of experiments using the device 16 compared to the conventional device 1 along the central visual axis 5 ( Fig.11 )'s longitudinal chromatic aberration (here: focus change A with respect to wavelength λ) ( Fig.11 ) and the Zernike coefficient Z for different viewing angles α at a wavelength of 546 nm 11Spherical aberration ( Fig.12 Here, the solid line 38 or 41 with circles corresponds to the results of the device 16 according to the invention, the dashed line 39 or 42 with triangles corresponds to the conventional device 1, and the dotted line 40 or 43 with diamonds corresponds to the results of the implanted IOL 8.

[0099] If desired, additional optical elements may also be provided along the central visual axis 5, for example in order to correct aberrations or to extend the possible viewing angle α for examining the IOL 8. Furthermore, alternatively, the device 16 may also be constructed completely or partially with non-rotationally symmetrical lenses, for example, the aspherical lens surfaces of the corneal optics 18 and / or the eyepiece optics 20 described herein may be replaced by a system of multiple spherical lens surfaces that achieve similar optical effects.

[0100] In particular, by means of an arrangement consisting of two parallel devices 16 it is of course possible to examine two IOLs 8 simultaneously and in binocular (stereoscopic) vision.

[0101] In general, the eyepiece optics 20 , optionally in conjunction with the corneal optics 18 , may be used in any apparatus for examining vision through an IOL 8 .

[0102] The invention is not limited to the embodiments shown, but comprises all variants, modifications and combinations falling within the scope of the appended claims.

Claims

1. A device for checking vision through an artificial lens (8), the device comprising a carrier (17) which supports, in succession from distal to proximal on a central visual axis (5), a corneal optic (18), a holding device (19) for the artificial lens (8) and an eyepiece optic (20), It is characterized in that The eyepiece optical device (20) comprises a correction lens (23) at a distal end and a diverging lens (24) and a converging lens (25) at a proximal end relative to the distal end, The correction lens (23) has a concave lens surface (26) at the distal end and a convex lens surface (27) at the proximal end.

2. The device according to claim 1, characterized in that At least one of the lens surfaces (28, 29) of the diverging lens and the converging lens (24, 25) facing each other is an aspherical surface.

3. The device according to claim 2, characterized in that At least one of the lens surfaces (28, 29) of the diverging lens and the converging lens (24, 25) facing each other is an aspherical surface of at least fourth order.

4. The device according to claim 3, characterized in that The height of the arrow (z1) measured away from the vertex plane (33) of the aspheric surface is selected as follows: Where A4<0, in z1 is the height of the arrow measured from the distal end to the proximal end, ρ vertex curvature, r is the radial distance from the central visual axis (5), and A2, A4 are preset coefficients, wherein when the aspheric surface is the lens surface of the converging lens (24), A2>0, and when the aspheric surface is the lens surface of the diverging lens (25), A2<0.

5. The device according to any one of claims 2 to 4, characterized in that The aspherical surface is a lens surface (29) at the distal end of the converging lens (25).

6. The device according to any one of claims 2 to 5, characterized in that The lens surface (34) of the converging lens or diverging lens (25, 24) opposite to the aspherical surface is flat.

7. The device according to any one of claims 1 to 6, characterized in that At least one of the cornea optics and the eyepiece optics (18, 20) has an achromatic lens (21, 22; 24, 25) or an apochromatic lens.

8. The device according to any one of claims 1 to 7, characterized in that The corneal optical device (18) comprises a corneal diverging lens (21) and a corneal converging lens (22).

9. The device according to claims 7 and 8, characterized in that The corneal diverging lens (21) and the corneal converging lens (22) have different Abbe numbers, and / or the converging lens and the diverging lens (24, 25) of the eyepiece optical device (20) have different Abbe numbers.

10. The device according to claim 9, characterized in that The lens surface (36) at the distal end of the corneal converging lens (22) is an aspherical surface of at least fourth order.

11. The device according to claim 10, characterized in that The arrow height (z2) of the distal lens surface measured from the vertex plane (37) of the distal lens surface (36) of the corneal convergence lens (22) is selected as follows: Where A2>0 and A4<0, in z2 is the height of the arrow measured from the distal end to the proximal end, ρ vertex curvature, r is the radial distance from the central visual axis (5), and A2 and A4 are preset coefficients.

12. The device according to any one of claims 1 to 11, characterized in that The distal and proximal lens surfaces (26, 27) of the correction lens (23) are spherical surfaces, wherein the radius of curvature of the distal lens surface (26) of the correction lens (23) is numerically smaller than the radius of curvature of the proximal lens surface (27) of the correction lens (23).

13. The device according to any one of claims 1 to 12, characterized in that At least one of the elements: a corneal optical device (18), a retaining device (19) and an eyepiece optical device (20) is supported on the carrier (17) in an adjustably manner along the central visual axis (5) and / or transversely to the central visual axis (5).

14. The device according to any one of claims 1 to 13, characterized in that The holding device (19) is designed to receive the artificial lens (8) in an exchangeable manner.

15. Use of an eyepiece optical device (20) in an apparatus (16) for examining vision through an artificial lens (8), the eyepiece optical device comprising a correction lens (23) at a distal end and a diverging lens (24) and a converging lens (25) at a proximal end relative to the distal end, wherein the correction lens (23) has a concave lens surface (26) at a distal end and a convex lens surface (27) at a proximal end, and wherein at least one of the lens surfaces (28, 29) of the diverging lens and the converging lens (24, 25) facing each other is preferably aspherical.

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