Ophthalmologic information processing device, ophthalmologic device, ophthalmologic information processing method, and program

Abstract

Disclosed is an ophthalmic information processing device which calculates the diopter of an eye to be examined on the basis of wavefront aberration information obtained by measuring wavefront aberration of the eye to be examined, the eye to be examined being provided with an intraocular lens. The ophthalmic information processing apparatus includes an acquisition section and a calculation section. The acquisition unit acquires at least intraocular lens information indicating optical characteristics of an intraocular lens. The calculation unit changes a diopter calculation processing method in response to the intraocular lens information, and calculates the diopter of the eye to be examined.

Description

Technical Field

[0001] The present invention relates to an ophthalmologic information processing device, an ophthalmologic device, an ophthalmologic information processing method, and a program. Background Art

[0002] When cataracts develop, cataract surgery is usually performed. During cataract surgery, the contents of the lens capsule are removed and an intraocular lens (Intraocular Lens: hereinafter referred to as IOL) is implanted in the lens capsule. There are various types of IOLs. The subject needs to consider the contrast, brightness, distance vision, near vision, etc. of the image to select the appropriate type of IOL. After the operation, the refractive power of the subject's eye wearing the IOL is measured to confirm the visual status, vision recovery, etc.

[0003] Several ophthalmic devices for examining an eye to be examined wearing such an IOL have been proposed. For example, Patent Document 1 discloses a method of obtaining a transmissive image of the eye to be examined and determining whether the eye to be examined wears an IOL based on the obtained transmissive image. For example, Patent Document 2 discloses a method of using wavefront aberration information and using a group of point images of a part of the obtained point image to calculate the diopter. For example, Patent Document 3 discloses a method of projecting a ring pattern to measure the diopter of the eye to be examined wearing an IOL.

[0004] Patent Document 1: Japanese Patent Application Publication No. 2014-209994

[0005] Patent Document 2: Japanese Patent Application Publication No. 2017-213124

[0006] Patent Document 3: Japanese Patent Application Publication No. 2021-083940 Summary of the invention

[0007] In the conventional method, the diopter is calculated by a unified method regardless of the type of IOL. Therefore, there is a problem that the reliability of the calculation result of the diopter is reduced due to the difference in the type of IOL implanted in the eye to be inspected.

[0008] The present invention has been made in view of such circumstances, and one of its objects is to provide a new technology for improving the reliability of the calculation result of the refractive power of the subject's eye wearing an IOL.

[0009] One embodiment is an ophthalmic information processing device that calculates the diopter of a subject's eye based on wavefront aberration information obtained by measuring the wavefront aberration of the subject's eye wearing an intraocular lens. The ophthalmic information processing device includes: an acquisition unit that acquires at least intraocular lens information indicating the optical characteristics of the intraocular lens; and a calculation unit that changes the calculation processing method of the diopter in response to the intraocular lens information to calculate the diopter of the subject's eye.

[0010] An ophthalmologic apparatus according to another aspect of the embodiment includes: a measurement optical system including a focus lens and measuring a wavefront aberration of the eye to be inspected; and the ophthalmologic information processing apparatus described above.

[0011] An ophthalmic information processing method according to another embodiment of the present invention calculates the diopter of the eye to be inspected based on wavefront aberration information obtained by measuring the wavefront aberration of the eye to be inspected wearing an intraocular lens. The ophthalmic information processing method includes: an acquisition step of acquiring at least intraocular lens information indicating the optical characteristics of the intraocular lens; and a calculation step of changing the diopter calculation processing method in response to the intraocular lens information to calculate the diopter of the eye to be inspected.

[0012] A program according to another aspect of the embodiment causes a computer to execute each step of the above-described ophthalmologic information processing method.

[0013] According to the present invention, it is possible to provide a new technology for improving the reliability of the calculation result of the refractive power of the eye to be inspected wearing an IOL. BRIEF DESCRIPTION OF THE DRAWINGS

[0014] Figure 1 It is a schematic diagram showing a configuration example of the optical system of the ophthalmologic apparatus according to the first embodiment.

[0015] Figure 2 It is a schematic diagram showing a configuration example of the optical system of the ophthalmologic apparatus according to the first embodiment.

[0016] Figure 3 It is a schematic diagram showing a configuration example of the optical system of the ophthalmologic apparatus according to the first embodiment.

[0017] Figure 4 It is a schematic diagram showing a configuration example of the optical system of the ophthalmologic apparatus according to the first embodiment.

[0018] Figure 5 This is a diagram for explaining the operation of the ophthalmologic apparatus according to the first embodiment.

[0019] Figure 6 This is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to the first embodiment.

[0020] Figure 7 This is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to the first embodiment.

[0021] Figure 8 This is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to the first embodiment.

[0022] Fig. 9 This is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to the first embodiment.

[0023] Fig.10 This is a schematic diagram for explaining the multifocal refractive IOL according to the first embodiment.

[0024] Fig.11 This is a schematic diagram for explaining the multifocal refractive IOL according to the first embodiment.

[0025] Fig.12 This is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to the first embodiment.

[0026] Fig.13 This is a schematic diagram for explaining the multifocal diffractive IOL according to the first embodiment.

[0027] Fig.14 This is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to the first embodiment.

[0028] Fig.15 This is a schematic diagram for explaining the extended depth of field IOL according to the first embodiment.

[0029] Fig.16 This is a flowchart of an operation example of the ophthalmologic apparatus according to the first embodiment.

[0030] Fig.17 This is a flowchart of an operation example of the ophthalmologic apparatus according to the first embodiment.

[0031] Fig.18 This is a flowchart of an operation example of the ophthalmologic apparatus according to the first embodiment.

[0032] Fig.19 This is a flowchart of an operation example of the ophthalmologic apparatus according to the first embodiment.

[0033] Fig. 20 This is a flowchart of an operation example of the ophthalmologic apparatus according to the first embodiment.

[0034] Fig.21 This is a flowchart of an operation example of the ophthalmologic apparatus according to the first embodiment.

[0035] Fig. 22 This is a diagram for explaining the operation of the ophthalmologic apparatus according to the first embodiment.

[0036] Fig.23 This is a diagram for explaining the operation of the ophthalmologic apparatus according to the first embodiment.

[0037] Fig.24 This is a diagram for explaining the operation of the ophthalmologic apparatus according to the first embodiment.

[0038] Fig.25 This is a diagram for explaining the operation of the ophthalmologic apparatus according to the first embodiment.

[0039] Fig.26 This is a flowchart of an operation example of the ophthalmologic apparatus according to the second embodiment.

[0040] Fig. 27 This is a flowchart of an operation example of the ophthalmologic apparatus according to the second embodiment. DETAILED DESCRIPTION

[0041] The ophthalmologic information processing device, ophthalmologic device, ophthalmologic information processing method, and program of the present invention will be described in detail with reference to the accompanying drawings. In addition, the contents of the documents cited in this specification and any known techniques can be applied to the following embodiments.

[0042] The ophthalmic information processing device of the embodiment calculates the diopter of the eye to be inspected based on the wavefront aberration information obtained by measuring the wavefront aberration of the eye to be inspected wearing an IOL (intraocular lens). For example, the IOL is implanted into a lens capsule whose contents have been removed by surgery, so that the eye to be inspected can wear the IOL. The ophthalmic information processing device obtains at least IOL (intraocular lens) information representing the optical characteristics of the IOL, and changes the calculation processing method of the diopter according to the obtained IOL information, thereby calculating the diopter of the eye to be inspected.

[0043] The IOL information includes, for example, information indicating the number of focal points (the number of focal lengths) possessed by the IOL, information indicating the position of regions with different focal lengths in the IOL, information indicating whether the refraction phenomenon of light is used, information indicating whether the diffraction phenomenon of light is used, and at least one of information indicating whether there is a deep focus depth. Such IOL information can be determined according to a predetermined type of IOL. There are types of IOLs including monofocal type and multifocal type. The multifocal type includes multifocal diffractive type and multifocal refractive type. In several embodiments, the multifocal type includes an extended depth of focus (hereinafter referred to as EDoF) type. The user (subject, examiner, physician, etc.) uses an operating unit to specify or analyze an anterior ocular image or a translucent image of the subject's eye to identify the type of IOL implanted in the subject's eye, thereby acquiring such IOL information.

[0044] The ophthalmic information processing device changes the application method of the known Zernike polynomial fitting using the wavefront aberration information including the Hartmann image according to the IOL information, and calculates the refractive power corresponding to the type of IOL through the calculation processing method corresponding to the IOL information. The wavefront aberration information includes a Hartmann image obtained in a state where the subject's eye is focused corresponding to the average focal length of the IOL or a plurality of Hartmann images obtained in a state where the subject's eye is focused corresponding to a plurality of focal lengths of the IOL. The refractive power includes, for example, the spherical power (S), the cylindrical power (C), and the astigmatism axis angle (A). In several embodiments, the ophthalmic information processing device calculates the refractive power according to the focal length of the IOL.

[0045] In addition, at least one of the acquired multiple point images constituting the Hartmann image is separated into two or more separated point images according to the type of IOL. The two or more separated point images correspond to the focal lengths of the IOL, respectively. Therefore, the ophthalmic information processing device classifies the two or more separated point images corresponding to each point image into any one of two or more point image groups according to the IOL information, and calculates the diopter by a known method of performing Zernike polynomial fitting according to the point image group.

[0046] In some embodiments, an ophthalmic information processing device acquires pupil diameter information indicating the pupil diameter of the eye to be inspected, and calculates the diopter based on wavefront aberration information in an area defined based on the acquired pupil diameter information. For example, the ophthalmic information processing device normalizes the wavefront aberration information using the pupil diameter information, and calculates the diopter by a known method of performing Zernike polynomial fitting using the normalized wavefront aberration information.

[0047] Thus, the calculation processing method (calculation method) can be changed according to the type of IOL worn by the subject's eye to obtain the diopter, thereby improving the reliability of the calculation result of the diopter of the subject's eye wearing the IOL.

[0048] The ophthalmic device of the embodiment realizes the functions of the ophthalmic information processing device of the embodiment. The ophthalmic information processing method of the embodiment includes one or more steps for realizing the processing executed by the processor (computer) in the ophthalmic information processing device of the embodiment. The program of the embodiment causes the processor to execute each step of the ophthalmic information processing method of the embodiment. The recording medium (storage medium) of the embodiment is a non-temporary recording medium (storage medium) that can be read by a computer that records (stores) the program of the embodiment.

[0049] In this specification, "processor" refers to circuits such as CPU (Central Processing Unit), GPU (Graphics Processing Unit), ASIC (Application Specific Integrated Circuit), programmable logic devices (such as SPLD (Simple Programmable Logic Device), CPLD (Complex Programmable Logic Device), FPGA (Field Programmable Gate Array)). The processor realizes the functions of the implementation mode by reading and executing the program stored in the storage circuit or storage device.

[0050] Hereinafter, a case where an ophthalmic device as an embodiment has the functions of an ophthalmic information processing device of an embodiment will be described. In addition, the types of IOL include monofocal type, multifocal type, and EDoF type. In this case, unless otherwise specified, the case where the number of focal points of the multifocal IOL is "2" is described, but the structure of the embodiment can also be applied to the case where the number of focal points is three or more.

[0051] The ophthalmic device of the embodiment is capable of performing at least one of arbitrary subjective examinations and arbitrary objective measurements. In the subjective examination, information (such as visual marks) is presented to the subject, and the result is obtained based on the subject's response to the information. Subjective examinations include subjective refractive measurements such as far vision examinations, near vision examinations, contrast examinations, glare examinations, and visual field examinations. In objective measurements, light is irradiated to the subject's eye, and information related to the subject's eye is obtained based on the detection results of its return light. Objective measurements include measurements for obtaining characteristics of the subject's eye and imaging for obtaining images of the subject's eye. Objective measurements include objective refractive measurements, corneal shape measurements, intraocular pressure measurements, fundus imaging, tomographic imaging (OCT imaging) using optical coherence tomography (OCT), measurements using OCT, and the like.

[0052] Hereinafter, the ophthalmologic apparatus of the embodiment can perform a distance vision test, a near vision test, etc. as a subjective test, and can perform an objective refraction measurement based on wavefront aberration measurement, corneal shape measurement, etc. as an objective measurement. However, the structure of the ophthalmologic apparatus of the embodiment is not limited thereto.

[0053] <First Embodiment>

[0054] [structure]

[0055] The ophthalmic device of the first embodiment comprises: a face support portion fixed to a base; and a stand that can move forward, backward, up, down, left, and right relative to the base. A head that accommodates an optical system for inspecting (measuring) an eye to be inspected is provided on the stand. The face support portion and the head can be moved relative to each other by operating an operating portion arranged at a position on the examiner's side. In addition, the ophthalmic device can automatically move the face support portion and the head relative to each other by performing alignment described later.

[0056] (Optical System)

[0057] Figure 1 An example of the structure of the optical system of the ophthalmologic apparatus of the first embodiment is shown. The ophthalmologic apparatus 100 of the first embodiment is an optical system for inspecting the subject's eye E, and includes a Z alignment system 1, an XY alignment system 2, a cornea measurement system 3, a sight mark projection system 4, an observation system 5, an aberration measurement projection system 6, and an aberration measurement light receiving system 7. In addition, the ophthalmologic apparatus includes a processing unit 9.

[0058] (Processing unit 9)

[0059] The processing unit 9 controls each part of the ophthalmologic apparatus. In addition, the processing unit 9 can perform various calculation processes. The processing unit 9 includes a processor. The processing unit 9 reads and executes a program stored in a storage circuit or a storage device, for example, to thereby realize the functions of the embodiment.

[0060] (Observation system 5)

[0061] The observation system 5 captures a dynamic image of the anterior segment of the subject's eye E. For example, the return light from the anterior segment of the subject's eye E illuminated by light (for example, infrared light with a central wavelength of 950 nm) from a plurality of anterior segment illumination light sources 57 arranged at a position away from the optical axis of the observation system 5 passes through the objective lens 51, the dichroic mirror 52, and the opening of the aperture 53. The light passing through the opening of the aperture 53 passes through the half mirror 22, the relay lens 54, and is guided to the imaging lens 55. The imaging lens 55 images the light guided from the relay lens 54 on the light receiving surface of the area sensor (image sensor) 56. The light receiving surface of the area sensor 56 is arranged at a position that is substantially optically conjugate with the pupil of the subject's eye E. The area sensor 56 captures images and outputs signals at a predetermined rate. The output (image signal) of the area sensor 56 is input to the processing unit 9. The processing unit 9 displays the anterior segment image E' based on the image signal on the display screen 10a of the display unit 10. The anterior segment image E' is, for example, an infrared dynamic image.

[0062] (Z alignment system 1)

[0063] The Z alignment system 1 irradiates the subject's eye E with light (infrared light) for aligning the optical axis direction (front-back direction, Z direction) of the observation system 5. The light output from the Z alignment light source 11 is irradiated onto the cornea K of the subject's eye E, reflected by the cornea K, and guided to the imaging lens 12. The imaging lens 12 images the guided light on the light receiving surface of the linear sensor 13. When the position of the corneal vertex changes in the front-back direction, the projection position of the light relative to the linear sensor 13 changes. The output of the linear sensor 13 is input to the processing unit 9. The processing unit 9 calculates the position of the corneal vertex of the subject's eye E based on the projection position of the light relative to the linear sensor 13, and performs Z alignment based on this.

[0064] (XY alignment system 2)

[0065] The XY alignment system 2 irradiates the eye E to be inspected with light (infrared light) for alignment in a direction orthogonal to the optical axis of the observation system 5 (left-right direction (X direction), up-down direction (Y direction)). The XY alignment system 2 includes an XY alignment light source 21 disposed on an optical path branched from the observation system 5 by a half-reflecting mirror 22. The light output from the XY alignment light source 21 passes through a relay lens 23 and is reflected by the half-reflecting mirror 22. After the light reflected by the half-reflecting mirror 22 is focused on the front focal position of the objective lens 51 on the optical axis of the observation system 5, it passes through the dichroic mirror 52, is formed into parallel light by the objective lens 51, and is irradiated to the cornea K of the eye E to be inspected. The light reflected on the surface of the cornea K forms a Purkinje image near the reflection focal position on the corneal surface of the eye E to be inspected. The XY alignment light source 21 is arranged at a position that is substantially optically conjugate with the focal position of the objective lens 51. The reflected light reflected by the cornea K is guided to the area sensor 56 through the observation system 5. An image Br formed by a Purkinje image (bright spot) of light output from the XY alignment light source 21 is formed on the light receiving surface of the area sensor 56 .

[0066] like Figure 1 As shown, the processing unit 9 causes the display screen 10a to display the anterior ocular image E' including the bright spot image Br and the alignment mark AL. In the case of manual XY alignment, the examiner performs a movement operation of the optical system to guide the bright spot image Br into the alignment mark AL. In the case of automatic alignment, the processing unit 9 controls the mechanism for moving the optical system to eliminate the displacement of the bright spot image Br relative to the alignment mark AL.

[0067] (Corneal measurement system 3)

[0068] The corneal measurement system 3 projects an annular light beam (infrared light) for measuring the curvature of the cornea K onto the cornea K. The corneal plate 31 is arranged near the objective lens 51. A corneal ring light source 32 is provided on the back side (objective lens 51 side) of the corneal plate 31. The light from the corneal ring light source 32 is used to illuminate the corneal plate 31, thereby projecting the annular light beam onto the cornea K. The reflected light (corneal ring image) and the anterior eye image are detected together by the area sensor 56. The processing unit 9 performs known operations based on the corneal ring image to calculate the corneal curvature parameters. A placido ring plate composed of multiple rings can also be configured to replace the corneal ring. In this case, not only the curvature of the cornea can be measured, but also the shape of the cornea can be measured.

[0069] (Sight mark projection system 4)

[0070] The optotype projection system 4 presents various optotypes such as a fixation optotype and an optotype for subjective examination to the eye to be examined E. The optotype chart 42 displays a pattern representing the optotype under the control of the processing unit 9. The light (visible light) output from the light source 41 passes through the optotype chart 42, the relay lens 43 and the field lens 44, is reflected by the reflector 45, passes through the beam splitter 68, and is reflected by the dichroic mirror 52. The light reflected by the dichroic mirror 52 passes through the objective lens 51 and is projected onto the fundus Ef.

[0071] The moving unit 46 including the light source 41 and the optotype 42 can be moved along the optical axis of the optotype projection system 4. The position of the moving unit 46 is adjusted so that the optotype 42 is substantially optically conjugate with the fundus Ef.

[0072] The sight chart 42 can display a pattern representing a fixation mark for causing the subject's eye E to fixate under the control of the processing unit 9. By sequentially changing the display position of the pattern representing the fixation mark in the sight chart 42 to move the fixation position, it is possible to guide the eye to adjust its sight line and the subject's eye. Such a sight chart 42 includes an electronic display device using a liquid crystal panel, EL (field-induced luminescence), etc., a device (rotary type) that appropriately arranges any one of a plurality of sight marks drawn on a rotating glass plate, etc. on the optical axis. In addition, the sight chart projection system 4 can also include a glare inspection optical system for projecting glare onto the subject's eye E together with the sight mark.

[0073] In the case of a subjective examination, the processing unit 9 controls the moving unit 46 according to the result of the objective measurement. The processing unit 9 displays the optotype selected by the examiner or the processing unit 9 on the optotype chart 42. Thus, the optotype is presented to the subject. The subject responds to the optotype. The processing unit 9 receives the input of the response content and further performs control and calculation of the subjective examination value. For example, in the visual acuity measurement, the processing unit 9 selects and presents the next optotype according to the response to the Landolt ring, etc., and repeats this operation to determine the visual acuity value.

[0074] In objective measurement (objective refraction measurement, etc.), a landscape image is projected onto the fundus Ef. The subject is asked to fixate on the landscape image. Figure 1 While aligning, measure the diopter in the foggy vision state.

[0075] (Aberration measurement projection system 6, aberration measurement light receiving system 7)

[0076] The aberration measurement projection system 6 and the aberration measurement light receiving system 7 are used to measure the eyeball aberration characteristics of the subject's eye E. The aberration measurement projection system 6 projects a light beam (mainly infrared light) for measuring the eyeball aberration characteristics onto the fundus Ef. The aberration measurement light receiving system 7 receives the return light of the light beam from the fundus Ef of the subject's eye E. The eyeball aberration characteristics of the subject's eye E are obtained based on the light reception result of the return light received by the aberration measurement light receiving system 7.

[0077] The aberration measurement projection system 6 includes a light source 61 capable of outputting light in two or more wavelength regions with different central wavelengths. The light source 61 may be composed of a single light source capable of changing the wavelength region (central wavelength) of the output light, or may be composed of two or more light sources that switch to output light in different wavelength regions (central wavelengths). Figure 1 In the embodiment, the light source 61 includes: a light source 61A, which outputs light in a first wavelength region including a first central wavelength; and a light source 61B, which outputs light in a second wavelength region including a second central wavelength. For example, the first central wavelength is 560nm (visible region), and the second central wavelength is 840nm (near infrared region). In this case, the light source 61 outputs light output from either the light source 61A or the light source 61B. In several embodiments, the light path from the light source 61A is coupled with the light path from the light source 61B through a dichroic mirror, and the light source 61A and the light source 61B are controlled to be exclusively turned on. In several embodiments, the light path from the light source 61A is coupled with the light path from the light source 61B through a dichroic mirror, and a pluggable first shutter is provided between the light source 61A and the dichroic mirror, and a pluggable second shutter is provided between the light source 61B and the dichroic mirror.

[0078] Light sources (point light sources) 61A and 61B are light sources that can emit tiny point lights. Examples of light sources 61A and 61B include highly condensing super luminescent diodes (SLDs), but may also be highly condensing LDs (laser diodes) or high-brightness LEDs with small light emission diameters.

[0079] The moving unit 69 including the light source 61 is movable along the optical axis of the aberration measurement projection system 6. The light source 61 is arranged at a position substantially optically conjugate with the fundus Ef. The light (measurement light) output from the light source 61 passes through the relay lens 62 and the field lens 63, and is transmitted through the polarizing plate 64. The polarizing plate 64 transmits only the s-polarized component among the polarized components of the light output from the light source 61. The light transmitted through the polarizing plate 64 passes through the opening of the aperture 65, is reflected by the polarization beam splitter 66 that reflects the s-polarized component, passes through the rotating prism 67, and is reflected by the beam splitter 68. The light reflected by the beam splitter 68 is reflected by the dichroic mirror 52, passes through the objective lens 51, and is projected onto the fundus Ef.

[0080] Figure 2 An example of the wavelength selection characteristics of the beam splitter 68 is schematically shown. Figure 2 In the figure, the vertical axis represents the transmittance of light and the horizontal axis represents the wavelength.

[0081] For example, the beam splitter 68 reflects light in a wavelength region with a first wavelength λ1 as a center wavelength, light in a wavelength region with a second wavelength λ2 as a center wavelength, and light in a wavelength region with a third wavelength λ3 (0<λ1<λ2<λ3) as a center wavelength, and transmits light in other wavelength regions. For example, the first wavelength λ1 is the center wavelength (560nm) of light output by the light source 61A, the second wavelength λ2 is the center wavelength (840nm) of light output by the light source 61B, and the third wavelength λ3 is the center wavelength (950nm) of light output by the anterior ocular illumination light source 57.

[0082] Thus, the beam splitter 68 transmits the light from the sight mark projection system 4 and reflects the light from the light sources 61A and 61B of the aberration measurement projection system 6 and the return light thereof, thereby enabling good wavelength separation of the sight mark projection system 4, the aberration measurement projection system 6, and the aberration measurement light receiving system 7. Such a beam splitter 68 may be, for example, a wavelength selective reflector disclosed in Japanese Patent Application Laid-Open No. 2010-099354.

[0083] Alternatively, instead of arranging the light source at the position of the light source 61, the light from the light source 61 may be guided to the relay lens 62 by an optical fiber connecting the light source and the ophthalmic apparatus. In this case, the fiber end of the optical fiber is arranged at a position substantially optically conjugate with the fundus Ef.

[0084] The rotating prism 67 is used to average out unevenness in reflectance in blood vessels or lesion sites of the fundus Ef or to reduce speckle noise of the SLD light source.

[0085] The light incident on the eye E to be inspected no longer maintains its polarization state due to scattered reflection of the fundus, and the return light from the fundus Ef becomes a mixture of p-polarized components and s-polarized components. Such return light from the fundus Ef passes through the objective lens 51 and is reflected by the dichroic mirror 52 and the beam splitter 68. The return light reflected by the beam splitter 68 passes through the rotating prism 67 and is guided to the polarization beam splitter 66. The polarization beam splitter 66 transmits only the p-polarized component among the polarization components of the return light. The light of the p-polarized component passing through the polarization beam splitter 66 passes through the field lens 71, is reflected by the reflector 72, passes through the relay lens 73, and is guided to the moving unit 77. Since the light positively reflected on the surface of the objective lens 51 and the cornea K of the eye E to be inspected maintains s-polarization, it is reflected by the polarization beam splitter 66, and since it does not enter the aberration measurement light receiving system 7, the occurrence of ghosting can be reduced.

[0086] The moving unit 77 includes a collimating lens 74, a Hartmann plate 75, and an area sensor 76. The collimating lens 74 functions as a focusing lens by the movement of the moving unit 77. The area sensor 76 uses, for example, a CCD (Charge Coupled Device) image sensor or a CMOS (Complementary Metal Oxide Semiconductor) image sensor. The light guided to the moving unit 77 passes through the collimating lens 74 and is incident on the Hartmann plate 75. The Hartmann plate 75 is arranged at a position that is roughly optically conjugate with the pupil of the eye E to be examined. The moving unit 77 can move along the optical axis of the aberration measurement light receiving system 7. The moving unit 77 moves along the optical axis in accordance with the refractive power of the eye E to be examined, so that the fundus Ef is roughly optically conjugate with the front focus position of the collimating lens 74.

[0087] Figure 3 and Figure 4 An explanatory diagram showing a Hartmann plate 75 according to the embodiment. Figure 3 and Figure 4 The structure of the Hartmann plate 75 when viewed from the optical axis direction of the aberration measurement light receiving system 7 is schematically shown.

[0088] The Hartmann plate 75 generates a plurality of focused lights from the return light from the fundus Ef. Figure 3 and Figure 4 As shown, a plurality of micro lenses 75A are arranged in a grid pattern on the Hartmann plate 75. The Hartmann plate 75 divides incident light into a plurality of light beams and focuses each of the light beams.

[0089] For example, Figure 3 As shown, the Hartmann plate 75 has a structure in which a plurality of microlenses 75A are arranged on a glass plate by etching, molding, etc. In this case, the opening of each microlens can be made larger, and the signal strength can be improved.

[0090] In addition, if Figure 4 As shown, the Hartmann plate 75 may also have the following structure: a chromium shading film is formed around each microlens 75A to provide a shading portion 75B, and a plurality of microlenses 75A are arranged. The microlenses 75A are not limited to a square arrangement, but may be arranged on concentric circles, arranged at the vertices of a triangle, or arranged in a hexagonal arrangement.

[0091] The area sensor 76 is disposed at the focal position of the microlens 75A, and detects the light (convergent light) focused by the Hartmann plate 75. Figure 5 As shown in FIG. 1 , the light irradiation area a of the light receiving surface of the area sensor 76 and the pupil Ep of the eye E to be examined are 1 , …, b 1 ,…,c 1 , ... correspondingly, the microlens 75A of the Hartmann plate 75 forms a point image A 1 , …, B 1 ,…,C 1 ,…. As described above, when the fundus Ef is in a roughly optically conjugate relationship with the front focal position of the collimating lens 74, the interval between the centroid positions of the point images (or the peak positions of the brightness of the point images) formed on the light-receiving surface of the area sensor 76 is roughly equal to the distance between the lens centers of the microlenses 75A. The area sensor 76 detects the point image group formed by the microlenses 75A of the Hartmann plate 75. The processing unit 9 obtains a detection signal based on the point image group detected by the area sensor 76 and position information indicating the detection position of the point image group, and calculates the wavefront aberration of the light incident on the Hartmann plate 75 by analyzing the position of the point image formed by each microlens 75A. Thus, the eye aberration characteristics of the subject's eye E are calculated based on the interval between the point images. The processing unit 9 calculates the refractive power of the subject's eye E based on the calculated eye aberration characteristics.

[0092] The processing unit 9 can move the moving unit 69 and the moving unit 77 along the optical axis direction according to the calculated diopter, so that the light source 61 (light source 61A, 61B) and the fundus Ef are optically conjugated with the front focal position of the collimating lens 74. In addition, the processing unit 9 can move the moving unit 46 along the optical axis direction in conjunction with the movement of the moving units 69, 77.

[0093] In some embodiments, the ophthalmic device 100 can obtain a transillumination image of the subject's eye E. For example, one (or part) of the plurality of anterior ocular illumination light sources 57 is turned on to project light from a position away from the optical axis through the pupil to the fundus Ef, and the area sensor 56 receives the return light to obtain a transillumination image.

[0094] In some embodiments, the XY alignment light source 21 is turned on, light is projected to the fundus Ef through the pupil, and the area sensor 56 receives the return light to acquire a transillumination image. In this case, the XY alignment light source 21 may be an SLD or a high-brightness LED. For example, the XY alignment light source 21 may be configured such that light is output from the LD as the alignment light source during alignment, and light is output from the SLD or high-brightness LED as the illumination light source for acquiring a transillumination image during acquisition of a transillumination image.

[0095] (Structure of processing system)

[0096] The processing system of the ophthalmologic apparatus 100 according to the embodiment will be described.

[0097] Figure 6 A functional configuration example of the processing system of the ophthalmologic apparatus 100 is shown. Figure 6 An example of a functional block diagram of a processing system of an ophthalmic apparatus according to an embodiment is shown. Figure 6 In, with Figure 1 The same parts are denoted by the same reference numerals, and the description thereof will be appropriately omitted.

[0098] The processing unit 9 includes a control unit 110 and an arithmetic processing unit 120 . In addition, the ophthalmologic apparatus 100 includes a display unit 170 , an operation unit 180 , a communication unit 190 , and a moving mechanism 200 .

[0099] The moving mechanism 200 is a mechanism for moving the head that accommodates the optical systems such as the Z alignment system 1, the XY alignment system 2, the cornea measurement system 3, the sight mark projection system 4, the observation system 5, the aberration measurement projection system 6, and the aberration measurement light receiving system 7 in the forward, backward, upward, downward, and leftward and rightward directions. For example, the moving mechanism 200 is provided with an actuator that generates a driving force for moving the moving mechanism 200 and a transmission mechanism that transmits the driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is composed of, for example, a combination of gears, a gear and a pinion, etc. The control unit 110 (main control unit 111) controls the moving mechanism 200 by sending a control signal to the actuator.

[0100] (Control Unit 110)

[0101] The control unit 110 includes a processor and controls various parts of the ophthalmic device. The control unit 110 includes a main control unit 111 and a storage unit 112. The storage unit 112 stores a computer program for controlling the ophthalmic device in advance. The computer program includes a light source control program, a sensor control program, an optical system control program, a calculation processing program, and a user interface program. The main control unit 111 operates according to such a computer program, and the control unit 110 performs control processing.

[0102] The main control unit 111 performs various controls of the ophthalmic device as a measurement control unit. The control of the Z alignment system 1 includes the control of the Z alignment light source 11, the control of the linear sensor 13, etc. The control of the Z alignment light source 11 includes the lighting, extinguishing, and light intensity adjustment of the light source. The control of the linear sensor 13 includes the exposure adjustment, gain adjustment, and detection rate adjustment of the detection element. In this way, the lighting and non-lighting of the Z alignment light source 11 are switched or the light intensity is changed. The main control unit 111 imports the signal detected by the linear sensor 13, and determines the projection position of the light relative to the linear sensor 13 based on the imported signal. The main control unit 111 calculates the position of the corneal vertex of the subject's eye E based on the determined projection position, controls the moving mechanism 200 based on the position, and moves the head in the front-back direction (Z alignment).

[0103] The control of the XY alignment system 2 includes the control of the XY alignment light source 21, etc. The control of the XY alignment light source 21 includes the lighting, extinguishing, light intensity adjustment, etc. of the light source. Thus, the lighting and non-lighting of the XY alignment light source 21 are switched or the light intensity is changed. The main control unit 111 imports the signal detected by the area sensor 56, and determines the position of the bright spot image based on the return light from the XY alignment light source 21 according to the imported signal. The main control unit 111 controls the moving mechanism 200 to move the head in the left, right, up and down directions so as to eliminate the displacement of the position of the bright spot image relative to the predetermined target position (for example, the center position of the alignment mark) (XY alignment).

[0104] The cornea measurement system 3 is controlled by the cornea ring light source 32. The cornea ring light source 32 is controlled by the lighting, extinguishing, light intensity adjustment, etc. Thus, the lighting and non-lighting of the cornea ring light source 32 are switched or the light intensity is changed. The main control unit 111 causes the calculation processing unit 120 to perform a known calculation on the cornea ring image detected by the area sensor 56. Thus, the cornea shape parameters of the subject's eye E are obtained.

[0105] The control of the sight mark projection system 4 includes the control of the light source 41, the control of the sight mark chart 42, the movement control of the moving unit 46, etc. The control of the light source 41 includes the lighting, extinguishing, and light intensity adjustment of the light source. Thus, the lighting and non-lighting of the light source 41 are switched or the light intensity is changed. The control of the sight mark chart 42 includes the opening and closing of the display of the sight mark and the fixation mark, the switching of the display position of the fixation mark, etc. Thus, the sight mark and the fixation mark are projected onto the fundus Ef of the eye E to be examined. For example, the sight mark projection system 4 includes a moving mechanism that moves the moving unit 46 along the optical axis. The moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force in the same manner as the moving mechanism 200. The main control unit 111 controls the moving mechanism by sending a control signal to the actuator to move the moving unit 46 along the optical axis. Thus, the position of the moving unit 46 is adjusted so that the sight mark chart 42 is roughly optically conjugate with the fundus Ef.

[0106] The observation system 5 is controlled by the area sensor 56 and the anterior ocular illumination light source 57. The area sensor 56 is controlled by exposure adjustment, gain adjustment, detection rate adjustment, etc. of the area sensor 56. The main control unit 111 imports the signal detected by the area sensor 56 and causes the calculation processing unit 120 to perform processing such as image formation based on the imported signal. The anterior ocular illumination light source 57 is controlled by lighting, extinguishing, light intensity adjustment, etc. of the light source. Thus, the lighting and non-lighting of the anterior ocular illumination light source 57 are switched, or one or part of the anterior ocular illumination light source 57 is lit, or the light intensity of each light source is changed.

[0107] The control of the aberration measurement projection system 6 includes the control of the light sources 61A and 61B, the control of the rotating prism 67, the control of the moving unit 69, etc. The control of the light sources 61A and 61B includes the lighting, extinguishing, light quantity adjustment, etc. of the light sources. Thus, the lighting and non-lighting of the light sources 61A and 61B are switched, or the light quantity is changed, or the wavelength range of the light output by the light source 61 is changed. The control of the rotating prism 67 includes the rotation control of the rotating prism 67, etc. For example, a rotating mechanism for rotating the rotating prism 67 is provided, and the main control unit 111 rotates the rotating prism 67 by controlling the rotating mechanism. For example, the aberration measurement projection system 6 includes a moving mechanism for moving the moving unit 69 along the optical axis direction. The moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force in the same manner as the moving mechanism 200. The main control unit 111 controls the moving mechanism by sending a control signal to the actuator, so that the moving unit 69 moves along the optical axis direction.

[0108] The control of the aberration measurement light receiving system 7 includes the control of the area sensor 76, the movement control of the moving unit 77, etc. The control of the area sensor 76 includes the exposure adjustment, gain adjustment, detection rate adjustment, etc. of the area sensor 76. The main control unit 111 imports the signal detected by the area sensor 76, and causes the calculation processing unit 120 to perform calculation processing of the eye aberration characteristics according to the imported signal. For example, the aberration measurement light receiving system 7 includes a moving mechanism that moves the moving unit 77 along the optical axis direction. The moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force in the same manner as the moving mechanism 200. The main control unit 111 controls the moving mechanism by sending a control signal to the actuator, so that the moving unit 77 moves along the optical axis direction. The main control unit 111 controls the moving mechanism by sending a control signal to the actuator, so that the moving unit 77 moves along the optical axis direction.

[0109] The main control unit 111 as a display control unit can make the display unit 170 display various information. The information displayed on the display unit 170 includes objective measurement results (aberration measurement results) obtained using the optical system, subjective inspection results, images based on these results, information, etc. For example, the refractive power obtained by the calculation processing unit 120, the wavefront aberration map showing the distribution of wavefront aberrations, the simulation image showing the visual state, the visual acuity simulation result, etc. are displayed on the display unit 170. The main control unit 111 can make the display unit 170 display this information or identify and display part of it according to the multiple focal length areas of the IOL.

[0110] In addition, the main control unit 111 performs a process of writing data to the storage unit 112 and a process of reading data from the storage unit 112 .

[0111] (Storage Unit 112)

[0112] The storage unit 112 stores various data. Examples of the data stored in the storage unit 112 include subjective examination results, objective measurement results, image data of anterior ocular images, image data of Hartmann point images, information about the eye to be examined, and processing results of the calculation processing unit 120. The information about the eye to be examined includes information about the subject such as the patient ID and name, and information about the eye to be examined such as left / right eye identification information. In addition, the storage unit 112 stores various programs and data for operating the ophthalmologic apparatus.

[0113] (Calculation Processing Unit 120)

[0114] The calculation processing unit 120 includes a processor, and executes the following processing of each unit according to a computer program stored in a storage unit (or the storage unit 112 ) not shown.

[0115] Figure 7 Show Figure 6 A functional block diagram of a structural example of the operation processing unit 120.

[0116] The calculation processing section 120 includes a diopter calculation section 130 , a distribution information generation section 140 , and a simulation processing section 150 .

[0117] (Diopter Calculation Unit 130)

[0118] The refractive power calculation unit 130 calculates the refractive power of the eye E to be inspected by a calculation processing method corresponding to the type of IOL. The types of IOL include monofocal type, multifocal refractive type, multifocal diffractive type, and EDoF type. Therefore, the refractive power calculation unit 130 includes a first refractive power calculation unit 131, a second refractive power calculation unit 132, a third refractive power calculation unit 133, and a fourth refractive power calculation unit 134.

[0119] The first refractive power calculation section 131 performs a first refractive power calculation process in which the refractive power of the subject's eye E is calculated by a calculation processing method corresponding to a monofocal IOL. The second refractive power calculation section 132 performs a second refractive power calculation process in which the refractive power of the subject's eye E is calculated by a calculation processing method corresponding to a multifocal refractive IOL. The third refractive power calculation section 133 performs a third refractive power calculation process in which the refractive power of the subject's eye E is calculated by a calculation processing method corresponding to a multifocal diffractive IOL. The fourth refractive power calculation section 134 performs a fourth refractive power calculation process in which the refractive power of the subject's eye E is calculated by a calculation processing method corresponding to an EDoF IOL.

[0120] When each functional block constituting the first refractive power calculation section 131 , the second refractive power calculation section 132 , the third refractive power calculation section 133 , and the fourth refractive power calculation section 134 has the same function, they may be shared as appropriate.

[0121] (First Refractive Power Calculation Section 131)

[0122] When the IOL worn by the eye E to be inspected is a monofocal IOL, the first refractive power calculation section 131 calculates a single refractive power based on wavefront aberration information including the Hartmann image obtained by wavefront aberration measurement.

[0123] Figure 8 Show Figure 7 FIG. 1 is a functional block diagram of a configuration example of the first refractive power calculation unit 131 shown in FIG.

[0124] The first refractive power calculation section 131 includes a point image determination section 131A, a representative position determination section 131B, and a Zernike polynomial fitting processing section 131C.

[0125] The point image determination unit 131A determines the point images constituting the Hartmann image. The point image determination unit 131A determines the point images based on the brightness values ​​of the Hartmann image obtained by the area sensor 56. In some embodiments, before the point image determination unit 131A determines the point images, point image enhancement processing is performed on the Hartmann image.

[0126] The representative position determination unit 131B determines the representative position of the point image determined by the point image determination unit 131A. Examples of the representative position include the centroid position, the center position, the position in the point image closest to the center of the Hartmann image, the position in the point image farthest from the center of the Hartmann image, etc. In this embodiment, the representative position determination unit 131B determines the centroid position as the representative position.

[0127] The Zernike polynomial fitting processing unit 131C performs Zernike polynomial fitting processing based on the representative positions of the plurality of point images determined by the representative position determination unit 131B, and obtains the spherical power S, the astigmatism power C, and the astigmatism axis angle A as a single diopter. That is, the Zernike polynomial fitting processing unit 131C obtains the inclination of the light at the representative positions of the plurality of point images determined by the representative position determination unit 131B, and obtains the wavefront fitting formula by a known operation using the obtained inclination amount of the light. The obtained wavefront fitting formula is expressed using Zernike coefficients and Zernike polynomials. The wavefront aberration information is expressed using Zernike coefficients. At this time, the Zernike polynomial fitting processing unit 131C can normalize the wavefront aberration information using the pupil diameter of the subject's eye E or the pupil diameter of the model eye, as disclosed in, for example, Japanese Patent Application Laid-Open No. 2002-209854. The Zernike polynomial fitting processing unit 131C obtains the spherical power S, the astigmatism power C, and the astigmatism axis angle A from the low-order terms of the Zernike coefficients through known calculations. For example, the Zernike polynomial fitting processing unit 131C can calculate the diopter by the method disclosed in Japanese Patent Application Laid-Open No. 2002-209854 or Japanese Patent Application Laid-Open No. 2017-213124.

[0128] (Second Refractive Power Calculation Section 132)

[0129] When the IOL worn by the eye E to be inspected is a multifocal refractive IOL, the second refractive power calculation unit 132 calculates a plurality of refractive powers corresponding to a plurality of focal lengths of the IOL, respectively, based on the wavefront aberration information including the Hartmann image obtained by the wavefront aberration measurement. That is, the second refractive power calculation unit 132 calculates a plurality of refractive powers including a refractive power corresponding to a far point and a refractive power corresponding to a near point, according to the region corresponding to the focal length of the IOL.

[0130] Fig. 9 Show Figure 7 FIG. 1 is a functional block diagram of a configuration example of the second refractive power calculation unit 132 shown in FIG.

[0131] The second refractive power calculation section 132 includes a point image determination section 132A, a representative position determination section 132B, a point image group determination section 132C, and a Zernike polynomial fitting processing section 132D.

[0132] The point image identifying unit 132A identifies point images constituting the Hartmann image in the same manner as the point image identifying unit 131A. In some embodiments, before the point images are identified by the point image identifying unit 132A, point image enhancement processing is performed on the Hartmann image.

[0133] The representative position identifying unit 132B identifies the representative position (center of gravity position) of the point image identified by the point image identifying unit 132A, similarly to the representative position identifying unit 131B.

[0134] The point image group identification unit 132C classifies two or more separate point images separated from the point image to be formed into a point image group according to the focal length of the IOL.

[0135] The Zernike polynomial fitting processing unit 132D calculates the refractive power of the eye E according to the point image group determined by the point image group determination unit 132C, similarly to the Zernike polynomial fitting processing unit 131C.

[0136] Fig.10 and Fig.11 Point images acquired by the area sensor 56 are schematically shown corresponding to the lens areas of the multifocal refractive IOL according to the first embodiment. Fig.10 This is a diagram showing point images corresponding to a ring-zone type multifocal refractive IOL in which regions with different focal lengths are arranged concentrically. Fig.11 This is a diagram showing a point image corresponding to a sector-shaped multifocal refractive IOL in which regions with different focal lengths are arranged below a lens region.

[0137] When the number of focal points of the ring zone type multifocal refractive IOL is "2", for example, a near area capable of focusing at close range and a far area capable of focusing at far range are alternately arranged from the center to the outside. Fig.10In the embodiment, the near area NA1, the far area FA1, the near area NA2, the far area FA2, ..., the near area NA4 and the far area FA4 are alternately arranged from the center to the outside. When the number of focal points of the ring-band type multifocal refractive IOL is "3", similarly, the near area, the middle area that can focus at an intermediate distance between near and far, and the far area are sequentially arranged from the center to the outside. When the number of focal points of the ring-band type multifocal refractive IOL is 4 or more, similarly, the near area, two or more middle areas with different intermediate distances, and the far area are sequentially arranged from the center to the outside. In this example, the center side is configured as the near area, and the side away from the center is configured as the far area, but the center side can also be configured as the far area, and the side away from the center can be configured as the near area.

[0138] The second refractive power calculation unit 132 specifies a point image group included in a region corresponding to a predetermined focal length, and calculates the refractive power for each point image group based on wavefront aberration information obtained from the specified point image group.

[0139] When the number of focal points of the sector-shaped multifocal refractive IOL is "2", Fig.11 As shown, the near vision area NA1 is arranged below the lens area which is the distance vision area FA1. When the number of focal points of the sector-shaped multifocal refractive IOL is 3 or more, for example, one or more intermediate vision areas are arranged between the distance vision area FA1 and the near vision area NA1.

[0140] In this case, the second refractive power calculation unit 132 specifies a point image group included in a region corresponding to the focal length, similarly to the annular type, and calculates the refractive power for each point image group based on wavefront aberration information obtained from the specified point image group.

[0141] Thus, for example, the diopter can be calculated based on the point image group included in the near vision area, and the diopter can be calculated based on the point image group included in the distance vision area. In some embodiments, the diopter can be calculated based on the point image group included in one or more intermediate vision areas.

[0142] (Third Refractive Power Calculation Unit 133)

[0143] When the IOL worn by the subject's eye E is a multifocal diffractive IOL, the third refractive power calculation unit 133 calculates a plurality of refractive powers corresponding to a plurality of focal lengths of the IOL, respectively, based on the wavefront aberration information including the Hartmann image obtained by the wavefront aberration measurement. Specifically, the third refractive power calculation unit 133 classifies two or more separated point images separated from the point image constituting the Hartmann image according to the focal length of the IOL, and calculates a plurality of refractive powers including a refractive power corresponding to a far point and a refractive power corresponding to a near point according to the focal length based on the classified two or more separated point images.

[0144] Fig.12 Show Figure 7 1 is a functional block diagram of a configuration example of the third refractive power calculation unit 133 shown in FIG.

[0145] The third refractive power calculation section 133 includes an enhancement processing section 133A, a point image determination section 133B, a representative position determination section 133C, a point image group determination section 133D, and a Zernike polynomial fitting processing section 133E.

[0146] The enhancement processing unit 133A performs enhancement processing on the point images in the Hartmann image. For example, the enhancement processing unit 133A increases the contrast of the Hartmann image and removes a portion with a saturated brightness value.

[0147] The point image determination unit 133B determines the point images constituting the Hartmann image in substantially the same manner as the point image determination unit 131A. Specifically, the point image determination unit 133B determines two or more separated point images separated from the point images constituting the Hartmann image. In this case, the point image determination unit 133B determines one or more separated point images on the far point side by analyzing the Hartmann image, and determines the remaining one or more separated point images on the near point side by analyzing the Hartmann image enhanced by the enhancement processing unit 133A. That is, the point image determination unit 133B determines point images above a predetermined first brightness value as separated point images on the far point side based on the Hartmann image, and determines point images above a predetermined second brightness value as separated point images on the near point side in the Hartmann image from which the portion with saturated brightness value is removed by increasing the contrast. Thus, it becomes easy to determine the separated point images on the near point side whose contrast is reduced due to the multifocal diffractive IOL.

[0148] In some embodiments, the point image identification unit 133B identifies one or more separated point images on the far point side and one or more separated point images on the near point side by analyzing the Hartmann image enhanced by the enhancement processing unit 133A.

[0149] In some embodiments, wavefront aberration measurement is performed using light in the visible region (eg, light from the light source 61A) in order to easily determine a separated point image on the near point side.

[0150] The representative position determination unit 133C determines the representative position (center of gravity position) of the separated point images determined by the point image determination unit 133B, similarly to the representative position determination unit 131B.

[0151] The point image group determination unit 133D classifies the two or more separated point images determined by the representative position determination unit 133C into any one of the two or more point image groups corresponding to the focal length of the IOL. The point image group determination unit 133D classifies the two or more separated point images separated from one point image into any one of a point image group of separated point images of near points, a point image group of one or more separated point images corresponding to one or more midpoints, and a point image group of separated point images of far points in order of proximity to the center of the Hartmann image.

[0152] The Zernike polynomial fitting processing unit 133E calculates the refractive power of the eye E according to the point image group determined by the point image group determination unit 133D, similarly to the Zernike polynomial fitting processing unit 131C.

[0153] Fig.13 Point images acquired by the area sensor 56 are schematically shown corresponding to the lens areas of the multifocal diffractive IOL of the first embodiment. Fig.13 , set the number of focus points to "2".

[0154] The point images constituting the Hartmann image are separated into two or more separate point images according to the focal length of the IOL. Fig.13 As shown in FIG. 1 , when the number of focal points is "2", the point image PI1 is separated into a separated point image (near point image) Pn1 close to the center of the Hartmann image and a separated point image (far point image) Pf1 far from the center of the Hartmann image based on the point image originally to be formed. Depending on the structure of the optical system, the point image PI1 may be separated by taking the separated point image close to the center of the Hartmann image as the far point image Pf1 and taking the separated point image far from the center of the Hartmann image as the near point image Pn1.

[0155] The third refractive power calculation unit 133 classifies the determined two or more separated point images into any one of two or more point image groups corresponding to the focal length of the IOL, and calculates the refractive power for each point image group. Fig.13 In the embodiment, the point image group determination unit 133D classifies the two separated point images corresponding to each point image constituting the Hartmann image into a point image group of near points and a point image group of far points. The Zernike polynomial fitting processing unit 133E calculates the diopter according to the point image group based on the wavefront aberration information obtained from the classified point image group. The third diopter calculation unit 133 can calculate the diopter according to the point image group as described above according to the Hartmann image.

[0156] (Fourth Refractive Power Calculation Unit 134)

[0157] When the IOL worn by the eye E to be inspected is an EDoF type IOL, the fourth refractive power calculation unit 134 determines two separated point images corresponding to the point images constituting the Hartmann image based on the wavefront aberration information including the Hartmann image obtained by the wavefront aberration measurement, classifies the determined separated point images into one of two point image groups, and calculates the refractive power according to the point image group based on the wavefront aberration information obtained from the classified point image group. Specifically, the fourth refractive power calculation unit 134 classifies two foci of a fitting ellipse determined by performing ellipse fitting on a plurality of point images constituting the Hartmann image, according to the focal length, and calculates a plurality of refractive powers including a refractive power corresponding to a far point and a refractive power corresponding to a near point according to the focal length based on the classified two or more separated point images.

[0158] Fig.14 Show Figure 7 1 is a functional block diagram of a configuration example of the fourth refractive power calculation unit 134 shown in FIG.

[0159] The fourth refractive power calculation section 134 includes a point image determination section 134A, an ellipse fitting processing section 134B, a point image group determination section 134C, and a Zernike polynomial fitting processing section 134D.

[0160] The point image identifying unit 134A identifies point images constituting the Hartmann image similarly to the point image identifying unit 131A. In some embodiments, before the point images are identified by the point image identifying unit 134A, point image enhancement processing is performed on the Hartmann image.

[0161] The ellipse fitting processing unit 134B performs a known ellipse fitting process on each of the plurality of point images determined by the point image determining unit 134A to determine a plurality of fitted ellipses, and determines two focal points of each of the plurality of determined fitted ellipses.

[0162] The point image group determination unit 134C determines the focus close to the center of the Hartmann image among the two foci of the fitting ellipse determined by the ellipse fitting processing unit 134B as a near point image, and determines the focus far from the center of the Hartmann image as a far point image. The point image group determination unit 134C classifies the plurality of near point images and the plurality of far point images determined according to the plurality of fitting ellipses into a point image group of near point images and a point image group of far point images.

[0163] The Zernike polynomial fitting processing unit 134D calculates the refractive power of the eye E according to the point image group determined by the point image group determination unit 134C, similarly to the Zernike polynomial fitting processing unit 131C.

[0164] Fig.15 Point images acquired by the area sensor 56 are schematically shown corresponding to the lens area of ​​the EDoF IOL according to the first embodiment.

[0165] The point image identification unit 134A identifies the point image by analyzing the Hartmann image. At this time, the point images constituting the Hartmann image are images extending in a direction connecting the far point and the near point (blurred images) due to the deep focal depth.

[0166] When the point images are arranged in a ring-shaped or fan-shaped manner like a multifocal refractive IOL, the calculation processing unit 120 can calculate the diopter according to the point image group like a multifocal refractive IOL through the second refractive power calculation unit 132. When the point images are separated into two or more separated point images like a multifocal diffractive IOL, the calculation processing unit 120 can calculate the diopter according to the point image group like a multifocal diffractive IOL through the third refractive power calculation unit 133.

[0167] When the shape of the point image is an ellipse, the ellipse fitting processing unit 134B performs ellipse fitting processing on the shape of the point image PI2 and determines the fitting ellipse AC1, and determines the two foci Pn2 and Pf2 of the determined fitting ellipse AC1. The point image group determination unit 134C determines the focus Pn2 close to the center of the Hartmann image among the two determined foci as the near point image, and determines the focus Pf2 far from the center of the Hartmann image as the far point image. Moreover, the point image group determination unit 134C similarly determines the two foci as the near point image and the far point image according to the plurality of point images, respectively, and classifies the determined plurality of near point images and the plurality of far point images into a point image group of near point images and a point image group of far point images. The Zernike polynomial fitting processing unit 134D calculates the diopter according to the point image group based on the wavefront aberration information obtained according to the classified point image group.

[0168] In addition, the diopter calculation unit 130 calculates the corneal refractive power, corneal astigmatism, and corneal astigmatism axis angle according to the corneal annular image acquired by the observation system 5. For example, the diopter calculation unit 130 calculates the corneal curvature radius of the strong principal meridian and the weak principal meridian of the anterior surface of the cornea by analyzing the corneal annular image, and calculates the parameters according to the corneal curvature radius.

[0169] (Distribution Information Generating Unit 140)

[0170] The distribution information generating unit 140 generates distribution information (wavefront aberration map) indicating the distribution of wavefront aberration according to the focal length of the IOL. The distribution information generating unit 140 generates distribution information based on the wavefront aberration information, for example, as disclosed in Japanese Patent Application Laid-Open No. 2002-209854. When the horizontal direction in the pupil of the eye E (or the light receiving surface of the area sensor 56) is set to the x direction and the vertical direction is set to the y direction, the distribution information generating unit 140 interpolates the wavefront aberration at each position (x, y) in the horizontal direction and the vertical direction by a known method, and generates distribution information indicating the two-dimensional distribution of the wavefront aberration.

[0171] When the IOL worn by the eye to be inspected E is a monofocal IOL, the distribution information generating section 140 generates distribution information indicating the distribution of the wavefront aberration based on the single wavefront aberration information.

[0172] When the IOL worn by the eye E to be inspected is a multifocal refractive IOL or a multifocal diffractive IOL, the distribution information generating unit 140 generates distribution information representing the distribution of the wavefront aberrations of the near point based on the wavefront aberration information obtained from the point image group on the nearest point side, and generates distribution information representing the distribution of the wavefront aberrations of the far point based on the wavefront aberration information obtained from the point image group on the farthest point side.

[0173] When the IOL worn by the eye E to be inspected is an EDoF type IOL, the distribution information generating unit 140 generates distribution information representing the distribution of the wavefront aberration of the near point based on the wavefront aberration information obtained from the point image group of the near point image, and generates distribution information representing the distribution of the wavefront aberration of the far point based on the wavefront aberration information obtained from the point image group of the far point image.

[0174] (Simulation Processing Unit 150)

[0175] The simulation processing unit 150 performs vision simulation. For example, the simulation processing unit 150 performs ray tracing processing on an eyeball having a wavefront aberration normalized using pupil diameter information, for example, object points converted from multiple diopters at intervals of 0.25D, thereby obtaining multiple images on the retinal surface. The simulation processing unit 150 determines the position of the clearest image or the position of the object point with the highest Strehl ratio among the multiple images corresponding to the obtained multiple diopters as the degree of the subject's eye E. In the case of multifocals, the position of the local clearest image or the position of the object point with the highest Strehl ratio within a certain range is determined as the degree of the subject's eye E at a distance or near, etc.

[0176] In addition, the simulation processing unit 150 can generate a simulated image representing the visual state of the sight mark. Examples of sight marks include blue road rings or images corresponding to a predetermined fixed distance. For example, the simulation processing unit 150 calculates the point spread function (Point Spread Function: hereinafter referred to as PSF) according to the wavefront aberration information normalized using the pupil diameter information according to multiple focal lengths of the IOL or one or more predetermined fixed distances by a known method. The simulation processing unit 150 calculates the simulated image of the sight mark when it is projected on the fundus Ef by convolution of the calculated PSF and the image data (brightness distribution) of the sight mark.

[0177] In some embodiments, the simulation processing unit 150 performs Fourier transform on the PSF to obtain an optical transfer function (OTF). The absolute value component of the amplitude of the OTF is the modulation transfer function (MTF), and its phase component is the phase transfer function (PTF). The simulation processing unit 150 calculates the convolution of the MTF with the image data of the sight mark, and calculates the convolution of the PTF with the image data of the sight mark. In addition, the simulation processing unit 150 performs an inverse Fourier transform on the calculation results of these convolutions to obtain a simulated image equivalent to the convolution of the PSF with the image data of the sight mark.

[0178] The processing performed by such a simulation processing unit 150 is disclosed in, for example, Japanese Patent Application Laid-Open No. 2004-337236.

[0179] The control unit 110 (main control unit 111) as a display control unit can cause the display unit 170 to display an image representing the visual state of the subject's eye E corresponding to the diopter calculated by the diopter calculation unit 130 according to the focal length of the IOL or one or more fixed distances. For example, the fixed distances include "infinity", "1m", "40cm" and "20cm". The image representing the visual state of the subject's eye E is a simulated image generated by the simulation processing unit 150.

[0180] In addition, the control unit 110 (main control unit 111) as a display control unit can cause the display unit 170 to display the simulation result of the visual acuity value of the subject's eye E according to the focal length of the IOL or one or more fixed distances. The simulation result of the visual acuity value is the degree (visual acuity value) of the subject's eye E calculated by the simulation processing unit 150.

[0181] (Display unit 170, operation unit 180)

[0182] The display unit 170 is a user interface unit that displays information under the control of the control unit 110 (main control unit 111). The display unit 170 includes Figure 1 The display unit 10 is shown.

[0183] The display unit 170 can display the processing results executed by the calculation processing unit 120 under the control of the control unit 110 (main control unit 111) as a display control unit. Examples of the processing results executed by the calculation processing unit 120 include one or more diopters calculated by the diopters calculation unit 130, distribution information generated by the distribution information generation unit 140, and simulation results executed by the simulation processing unit 150.

[0184] Examples of the one or more diopters calculated by the diopter calculation unit 130 include a single diopter calculated by the first diopter calculation unit 131, diopters of the number of focal points of the focal length (area) of the IOL calculated by the second diopter calculation unit 132 or the third diopter calculation unit 133, and diopters on the far point side and the near point side calculated by the fourth diopter calculation unit 134. In some embodiments, the diopters of the far point and the near point among the diopters of the number of focal points calculated by the second diopter calculation unit 132 or the third diopter calculation unit 133 are displayed on the display unit 170. In some embodiments, the difference between the diopters on the farthest point side and the closest point side calculated by the fourth diopter calculation unit 134 and calculated by the diopter calculation unit 130 is displayed on the display unit 170.

[0185] The operation unit 180 is used as a user interface unit to operate the ophthalmic device. The operation unit 180 includes various hardware keys (joystick, button, switch, etc.) provided on the ophthalmic device. In addition, the operation unit 180 may also include various software keys (buttons, icons, menus, etc.) displayed on the touch panel display screen 10a.

[0186] At least a part of the display unit 170 and the operation unit 180 may be integrally formed. A typical example thereof is a touch panel type display screen 10a.

[0187] (Communication Department 190)

[0188] The communication unit 190 has a function for communicating with an external device (not shown). The communication unit 190 may be provided in the processing unit 9, for example. The communication unit 190 has a configuration corresponding to a communication method between external devices.

[0189] The operation processing unit 120 is an example of an "ophthalmologic information processing device" of the embodiment. The communication unit 190 or the aberration measurement projection system 6 and the aberration measurement light receiving system 7 are an example of an "acquisition unit" of the embodiment. The aberration measurement projection system 6 and the aberration measurement light receiving system 7 are an example of a "measurement optical system" of the embodiment. The diopter calculation unit 130 is an example of a "calculation unit" of the embodiment. The control unit 110 (main control unit 111) is an example of a "display control unit" of the embodiment. The display unit 170 is an example of a "display unit" of the embodiment.

[0190] [Working example]

[0191] An operation example of the ophthalmologic apparatus according to the first embodiment will be described.

[0192] Figure 16 to Figure 21 A flowchart showing an operation example of the ophthalmologic apparatus 100 according to the first embodiment. Fig.161 is a flowchart showing an operation example of the ophthalmologic apparatus 100 for calculating the refractive power of the subject's eye E by a calculation processing method according to the type of IOL worn by the subject's eye E. FIG. Fig.17 Yes means Fig.16 Flowchart of an example of the operation of step S11. Fig.18 It is shown Fig.17 Flowchart of an example of the operation of step S22. Fig.19 Yes means Fig.17 Flow chart of an example of the operation of step S24. Fig. 20 Yes means Fig.17 Flow chart of an example of the operation of step S26. Fig.21 Yes means Fig.17 Flow chart of an example of the operation of step S28.

[0193] The storage unit 112 stores information for implementing Figure 16 to Figure 21 The main control unit 111 operates according to the computer program, thereby executing Figure 16 to Figure 21 Processing shown.

[0194] (S1: Obtain IOL information)

[0195] First, the main control unit 111 acquires the IOL information worn by the eye E to be inspected.

[0196] For example, the main control unit 111 controls the communication unit 190 to acquire IOL information indicating the type of IOL worn by the subject's eye E from the subject's electronic medical record information stored in an external device such as an ophthalmologic apparatus or a server connected via the communication unit 190 .

[0197] In some embodiments, the main control unit 111 acquires the IOL information from the type of IOL designated by the user's operation on the operation unit 180 .

[0198] In some embodiments, after the alignment described later is completed, the main control unit 111 controls the observation system 5 to acquire a transillumination image or anterior ocular image of the subject's eye E, controls the calculation processing unit 120 to analyze the transillumination image or the anterior ocular image, thereby distinguishing the type of IOL worn by the subject's eye E and acquiring IOL information. In this case, for example, the main control unit 111 turns on one of the plurality of anterior ocular illumination light sources 57, illuminates the fundus Ef with illumination light at a position away from the optical axis, and receives the return light thereof through the area sensor 56, thereby acquiring a transillumination image. Alternatively, for example, the main control unit 111 switches the XY alignment light source 21 to an SLD or a high-brightness LED, projects light on the fundus Ef, and receives the return light thereof through the area sensor 56, thereby acquiring a transillumination image. In addition, the main control unit 111 turns on the anterior ocular illumination light source 27, and receives the return light through the area sensor 56, thereby acquiring an anterior ocular image of the subject's eye E. The main control unit 111 can identify the type of IOL worn by the eye to be inspected E and acquire the IOL information by using the method disclosed in Japanese Patent Application Laid-Open No. 2014-209994, for example.

[0199] (S2: Obtain pupil diameter information)

[0200] Next, the main control unit 111 acquires pupil diameter information indicating the pupil diameter of the eye E to be inspected.

[0201] For example, the main control unit 111 controls the communication unit 190 to acquire the pupil diameter information of the subject's eye E from the subject's electronic medical record information stored in an external device such as an ophthalmologic apparatus or a server connected via the communication unit 190 .

[0202] In some embodiments, the main control unit 111 acquires pupil diameter information based on the pupil diameter designated by the user's operation content on the operation unit 180 .

[0203] In some embodiments, after the alignment described later is completed, the main control unit 111 adjusts the brightness of the light source 41 and the sight chart 42 of the sight chart projection system 4, controls the observation system 5 and obtains the anterior ocular image of the subject's eye E, controls the calculation processing unit 120 and analyzes the anterior ocular image, thereby determining the pupil diameter of the subject's eye E and obtaining pupil diameter information. Here, the brightness of the light source 41 and the sight chart 42 of the sight chart projection system 4 can be set, for example, to a brightness close to the daily brightness of the subject's eye E or the brightness of the desired state of the subject's eye E, or to a darker brightness so that any pupil diameter can be analyzed.

[0204] (S3: Alignment)

[0205] Next, with the subject's face fixed on a face support (not shown), the examiner performs a predetermined operation on the operation unit 180 , whereby the ophthalmic apparatus 100 starts presenting a fixation mark to the subject's eye E. Specifically, the main control unit 111 controls the mark projection system 4 to present a fixation mark to the subject's eye E.

[0206] Next, with the subject's face fixed to a face support (not shown), the examiner performs a predetermined operation on the operation unit 180, whereby the ophthalmic apparatus 100 performs alignment. As a result, the head moves to the inspection position of the subject's eye E through the XY alignment of the XY alignment system 2 and the Z alignment of the Z alignment system 1. The inspection position refers to a position where the subject's eye E can be inspected within a predetermined accuracy.

[0207] Specifically, the main control unit 111 obtains the imaging signal of the anterior ocular image formed on the light receiving surface of the area sensor 56, and causes the display unit 170 (display screen 10a of the display unit 10) to display the anterior ocular image E'. Thereafter, the head is moved to the inspection position of the eye E to be inspected through the XY alignment and Z alignment. The movement of the head is performed by the main control unit 111 according to the instruction of the main control unit 111, but may also be performed by the main control unit 111 according to the operation or instruction of the user.

[0208] After the alignment is completed, the main control unit 111 moves the moving unit 69 (light source 61), the moving unit 77, and the moving unit 46 along the optical axis to the position of the origin (e.g., the position corresponding to 0D). In some embodiments, the main control unit 111 moves the moving unit 69 (light source 61), the moving unit 77, and the moving unit 46 along the optical axis to the position of the origin (e.g., the position relative to 0D) before performing the alignment.

[0209] (S4: Obtaining Hartmann Image)

[0210] Next, the main control unit 111 performs preliminary measurement.

[0211] Specifically, the main control unit 111 turns on the light source 61B to irradiate the eye E with near-infrared light while presenting the optotype of the optotype chart 42 to the eye E to be inspected, and detects a Hartmann image (point image group) based on the return light from the eye E to be inspected by the area sensor 76 .

[0212] (S5: Calculate diopter)

[0213] Next, the main control unit 111 causes the diopter calculation unit 130 to calculate the diopter based on the intervals of the point images constituting the Hartmann image detected by the area sensor 76, and determines the movement amount of the moving unit 77 including the collimator lens 74 as the focus lens (equivalent to the movement amount of the focus lens) based on the calculated diopter. At this time, the diopter calculation unit 130 calculates the spherical power S as the diopter based on the intervals of the point images constituting the Hartmann image.

[0214] (S6: Move the focus lens)

[0215] The main control unit 111 moves the moving unit 77 (collimating lens 74 as a focus lens) along the optical axis to a position corresponding to the far point according to the movement amount corresponding to the diopter (spherical power S) calculated in step S5. In conjunction with this, the moving unit 46 and the moving unit 69 also move along the optical axis by the movement amount corresponding to the diopter.

[0216] (S7: Is this your first time?)

[0217] Next, the main control unit 111 determines whether the movement of the moving unit 77 and the like based on the preliminary measurement is the first time.

[0218] When it is determined that the movement is the first time (S7: Yes), the operation of the ophthalmologic apparatus 100 shifts to step S4. Thus, focus control can be performed with high accuracy based on the preliminary measurement.

[0219] When it is determined that the movement is not the first time ( S7 : No), the operation of the ophthalmologic apparatus 100 proceeds to step S8 .

[0220] (S8: Is it a multifocal diffractive IOL?)

[0221] When it is determined in step S7 that the movement is not the first time ( S7 : No), the main control unit 111 determines whether the IOL worn by the eye to be inspected E is a multifocal diffractive IOL based on the IOL information acquired in step S1 .

[0222] In step S8, when it is determined that the IOL worn by the subject's eye E is a multifocal diffractive IOL (S8: Yes), the operation of the ophthalmic apparatus 100 is transferred to step S9. In step S8, when it is determined that the IOL worn by the subject's eye E is not a multifocal diffractive IOL (S8: No), the operation of the ophthalmic apparatus 100 is transferred to step S10.

[0223] (S9: Switch light source)

[0224] In step S8 , when it is determined that the IOL worn by the subject's eye E is a multifocal diffractive IOL ( S8 : Yes), the main control unit 111 controls the light source 61 to switch the measurement light source from the light source 61B to the light source 61A.

[0225] (S10: Obtaining Hartmann Image)

[0226] In step S8, when it is determined that the IOL worn by the subject's eye E is not a multifocal diffractive IOL (S8: No), the main control unit 111 moves the moving unit 46 from the position corresponding to the far point moved in step S6 by a predetermined amount of diopter along the optical axis direction, so that the subject's eye E observes the sight mark in a foggy state. In addition, it may be determined that the subject's eye wearing the IOL does not have accommodation power, and the foggy vision function is omitted.

[0227] The main control unit 111 turns on the light source 61B to irradiate the eye E to be inspected with near-infrared light as a main measurement, and causes the area sensor 76 to detect a Hartmann image (point image group) based on the return light from the eye E to be inspected.

[0228] Alternatively, following step S9, the main control unit 111 turns on the light source 61A as a formal measurement to irradiate the subject's eye E with visible light, and causes the area sensor 76 to detect a Hartmann image (point image group) based on the return light from the subject's eye E. Thus, when the IOL worn by the subject's eye E is a multifocal diffractive IOL, wavefront aberration measurement is performed using visible light.

[0229] (S11: Calculate diopter)

[0230] Next, the main control unit 111 causes the diopter calculation unit 130 to calculate the diopter based on the intervals of the point images constituting the Hartmann image detected by the area sensor 76. The diopter calculation unit 130 calculates the diopter of the subject's eye E by a calculation processing method corresponding to the IOL information acquired in step S1. The diopter calculated in step S11 includes the spherical power (S), the cylindrical power (astigmatism power) (C), and the astigmatism axis angle (A). Step S11 will be described in detail later.

[0231] (S12: Output)

[0232] Next, the main control unit 111 causes the display unit 170 to display the diopter calculated in step S11. In some embodiments, the main control unit 111 controls the distribution information generating unit 140 to cause the display unit 170 to display the generated distribution information. In some embodiments, the main control unit 111 controls the simulation processing unit 150 to cause the display unit 170 to display the acquired simulation result. In some embodiments, the main control unit 111 causes the display unit 170 to display the measurement result obtained by the wavefront aberration measurement in association with the simulation result.

[0233] With the above, the operation of the ophthalmologic apparatus 100 ends (END).

[0234] according to Fig.17The process shown is executed Fig.16 Step S11.

[0235] (S21: Is it a monofocal IOL?)

[0236] exist Fig.16 In step S11 , first, the main control unit 111 determines whether the IOL worn by the eye to be inspected E is a monofocal IOL based on the IOL information acquired in step S1 .

[0237] In step S21, when it is determined that the IOL worn by the subject's eye E is a monofocal IOL (S21: Yes), the operation of the ophthalmologic apparatus 100 is transferred to step S22. In step S21, when it is determined that the IOL worn by the subject's eye E is not a monofocal IOL (S21: No), the operation of the ophthalmologic apparatus 100 is transferred to step S23.

[0238] (S22: First diopter calculation process)

[0239] In step S21, when it is determined that the IOL worn by the subject's eye E is a monofocal IOL (S21: Yes), the main control unit 111 controls the first refractive power calculation unit 131 to perform a first refractive power calculation process, in which the refractive power of the subject's eye E is calculated by a calculation method corresponding to the monofocal IOL based on the wavefront aberration information acquired in step S10. Step S22 will be described in detail later.

[0240] above, Fig.16 Step S11 ends (END).

[0241] (S23: Is it a multifocal refractive IOL?)

[0242] In step S21 , when it is determined that the IOL worn by the eye E is not a monofocal IOL ( S21 : No), the main control unit 111 determines whether the IOL worn by the eye E is a multifocal refractive IOL based on the IOL information acquired in step S1 .

[0243] In step S23, when it is determined that the IOL worn by the subject's eye E is a multifocal refractive IOL (S23: Yes), the operation of the ophthalmic apparatus 100 is transferred to step S24. In step S23, when it is determined that the IOL worn by the subject's eye E is not a multifocal refractive IOL (S23: No), the operation of the ophthalmic apparatus 100 is transferred to step S25.

[0244] (S24: Second diopter calculation process)

[0245] In step S23, when it is determined that the IOL worn by the subject's eye E is a multifocal refractive IOL (S23: Yes), the main control unit 111 controls the second refractive power calculation unit 132 to perform a second refractive power calculation process, in which the refractive power of the subject's eye E is calculated by a calculation processing method corresponding to the multifocal refractive IOL based on the wavefront aberration information acquired in step S10. Step S24 will be described in detail later.

[0246] above, Fig.16 Step S11 ends (END).

[0247] (S25: Is it a multifocal diffractive IOL?)

[0248] In step S23 , when it is determined that the IOL worn by the eye E is not a multifocal refractive IOL ( S23 : No), the main control unit 111 determines whether the IOL worn by the eye E is a multifocal diffractive IOL based on the IOL information acquired in step S1 .

[0249] In step S25, when it is determined that the IOL worn by the subject's eye E is a multifocal diffractive IOL (S25: Yes), the operation of the ophthalmic apparatus 100 is transferred to step S26. In step S25, when it is determined that the IOL worn by the subject's eye E is not a multifocal diffractive IOL (S25: No), the operation of the ophthalmic apparatus 100 is transferred to step S27.

[0250] (S26: Third diopter calculation process)

[0251] In step S25, when it is determined that the IOL worn by the subject's eye E is a multifocal diffractive IOL (S25: Yes), the main control unit 111 controls the third refractive power calculation unit 133 to perform a third refractive power calculation process, in which the refractive power of the subject's eye E is calculated by a calculation process method corresponding to the multifocal diffractive IOL based on the wavefront aberration information acquired in step S10. Step S26 will be described in detail later.

[0252] above, Fig.16 Step S11 ends (END).

[0253] (S27: Is it an EDoF IOL?)

[0254] In step S25 , when it is determined that the IOL worn by the eye E is not a multifocal diffractive IOL ( S25 : No), the main control unit 111 determines whether the IOL worn by the eye E is an EDoF IOL based on the IOL information acquired in step S1 .

[0255] In step S27, when it is determined that the IOL worn by the subject's eye E is an EDoF IOL (S27: Yes), the operation of the ophthalmologic apparatus 100 shifts to step S28. In step S27, when it is determined that the IOL worn by the subject's eye E is not an EDoF IOL (S27: No), the operation of the ophthalmologic apparatus 100 ends (END).

[0256] (S28: Fourth diopter calculation process)

[0257] In step S27, when it is determined that the IOL worn by the subject's eye E is an EDoF type IOL (S27: Yes), the main control unit 111 controls the fourth refractive power calculation unit 134 to perform a fourth refractive power calculation process, in which the refractive power of the subject's eye E is calculated by a calculation processing method corresponding to the EDoF type IOL based on the wavefront aberration information acquired in step S10. Step S28 will be described in detail later.

[0258] After step S28, Fig.16 Step S11 ends (END).

[0259] exist Fig.17 In step S22, the first refractive power calculation unit 131 calculates Fig.18 The illustrated flow executes the first refractive power calculation process.

[0260] (S31: Determine point image)

[0261] exist Fig.17 In step S22 , first, the main control unit 111 controls the point image specifying unit 131A to specify the point images constituting the Hartmann image acquired in step S10 .

[0262] (S32: Determine representative position)

[0263] Next, the main control unit 111 controls the representative position determination unit 131B to determine the representative position (here, the centroid position) of the point image determined in step S31 .

[0264] (S33: Zernike polynomial fitting process)

[0265] Next, the main control unit 111 controls the Zernike polynomial fitting processing unit 131C to perform Zernike polynomial fitting processing based on the representative positions of the plurality of point images determined in step S32 and the pupil diameter information acquired in step S2, thereby calculating wavefront aberration information (wavefront fitting formula) represented by Zernike coefficients and Zernike polynomials. The Zernike polynomial fitting processing unit 131C normalizes the calculated wavefront aberration information using the pupil diameter information acquired in step S2.

[0266] (S34: Calculation of diopter (SCA))

[0267] Next, the main control unit 111 controls the first diopter calculation unit 131 to obtain the spherical power S, the astigmatism power C, and the astigmatism axis angle A through known calculations based on the Zernike coefficients obtained by the Zernike polynomial fitting process performed in step S33.

[0268] above, Fig.17 The first refractive power calculation process in step S22 ends (END).

[0269] exist Fig.17 In step S24, the second diopter calculation unit 132 calculates the Fig.19 The second diopter calculation process is performed according to the flow shown.

[0270] (S41: Determine point image)

[0271] exist Fig.17 In step S24, first, the main control unit 111 controls the point image determination unit 132A to determine the point images constituting the Hartmann image acquired in step S10. In some embodiments, the main control unit 111 controls the second refractive power calculation unit 132 to control the point image determination unit 132A as described above after performing point image enhancement processing on the Hartmann image acquired in step S10.

[0272] (S42: Determine representative position)

[0273] Next, the main control unit 111 controls the representative position determination unit 132B to determine the representative position (here, the centroid position) of the point image determined in step S41 .

[0274] (S43: Determine point image group)

[0275] Next, the main control unit 111 controls the point image group determination unit 132C to determine, based on the representative position determined in step S42, in which region of the multiple regions predetermined according to the focal length of the IOL the point images constituting the Hartmann image are included. Here, if the position of the IOL within the pupil can be determined, then the positional relationship indicating where the multiple regions (number of focal regions) of each focal length of the IOL are respectively configured in the Hartmann image is known. Therefore, the point image group determination unit 132C can determine in which region the representative position of the point image is configured, based on the type of IOL determined based on the IOL information. The point image group determination unit 132C classifies the point images according to the focal length (each region) of the IOL (refer to Fig.10 and Fig.11 ). The point image group identification unit 132C may identify the point image group by identifying a region where the interval between point images is narrower than a predetermined reference interval and a region where the interval between point images is wider than a predetermined reference interval.

[0276] For example, when the number of focal points of the IOL worn by the eye E to be inspected is "2", the point image group determination unit 132C determines a point image group including one or more point images belonging to the near vision area and a point image group including one or more point images belonging to the far vision area. For example, when the number of focal points of the IOL worn by the eye E to be inspected is "3", the point image group determination unit 132C determines a point image group including one or more point images belonging to the near vision area, a point image group including one or more point images belonging to one or more intermediate vision areas, and a point image group including one or more point images belonging to the far vision area. For example, when the number of focal points of the IOL worn by the eye E to be inspected is four or more, the point image group determination unit 132C determines a point image group including one or more point images belonging to the near vision area, a point image group including one or more point images belonging to two or more intermediate vision areas, and a point image group including one or more point images belonging to the far vision area.

[0277] (S44: Execute Zernike polynomial fitting process according to point image group)

[0278] Next, the main control unit 111 controls the Zernike polynomial fitting processing unit 132D to perform Zernike polynomial fitting processing according to the point image group determined in step S43, thereby calculating wavefront aberration information (wavefront fitting formula) represented by Zernike coefficients and Zernike polynomials according to the point image group. The Zernike polynomial fitting processing unit 132D uses the pupil diameter information acquired in step S2 to normalize the wavefront aberration information calculated according to the point image group.

[0279] (S45: Calculate the diopter according to the point image group (SCA))

[0280] Next, the main control unit 111 controls the second refractive power calculation unit 132 to calculate the spherical power S, astigmatism power C and astigmatism axis angle A according to the point image group through known operations based on the Zernike coefficients obtained by the Zernike polynomial fitting process performed according to the point image group in step S44.

[0281] above, Fig.17 The second refractive power calculation process in step S24 ends (END).

[0282] exist Fig.17 In step S26, the third diopter calculation unit 133 calculates Fig. 20 The illustrated flow executes the third diopter calculation process.

[0283] (S51: Enhancement Process)

[0284] exist Fig.17In step S26, first, the main control unit 111 controls the enhancement processing unit 133A to perform point image (separated point image) enhancement processing on the Hartmann image acquired in step S10. Thus, it is easy to identify two or more separated point images (especially, separated point images on the near point side) formed by separating the point images constituting the Hartmann image.

[0285] (S52: Determine point image)

[0286] Next, the main control unit 111 controls the point image specifying unit 133B to specify the separate point images constituting the Hartmann image on which the enhancement process of the separate point images has been performed in step S51 .

[0287] (S53: Determine representative position)

[0288] Next, the main control unit 111 controls the representative position determination unit 133C to determine the representative position (here, the centroid position) of the separated point image determined in step S51 .

[0289] (S54: Determine point image group)

[0290] Next, the main control unit 111 controls the point image group determination unit 133D to determine the point image group according to the focal length of the IOL based on the representative position separation point image determined in step S53. The point image group determination unit 132C classifies the separation point image determined in step S52 into any one of two or more point image groups determined according to the type of IOL determined based on the IOL information.

[0291] For example, when the number of focal points of the IOL worn by the eye E to be inspected is "2", the point image group determination unit 133D classifies the multiple separated point images determined in step S52 into any one of the point image group of separated point images of near points and the point image group of separated point images of far points, thereby determining the point image group of separated point images of near points and the point image group of separated point images of far points. For example, when the number of focal points of the IOL worn by the eye E to be inspected is "3", the point image group determination unit 133D classifies the multiple separated point images determined in step S52 into any one of the point image group of separated point images of near points, the point image group of separated point images of midpoints, and the point image group of separated point images of far points, thereby determining the point image group of separated point images of near points, the point image group of separated point images of midpoints, and the point image group of separated point images of far points. For example, when the number of focal points of the IOL worn by the eye E to be inspected is four or more, the point image group determination unit 133D classifies the multiple separated point images determined in step S52 into any one of a point image group of separated point images of near points, two or more point image groups of separated point images of two or more midpoints, and a point image group of separated point images of far points, thereby determining the point image group of separated point images of near points, two or more point image groups of separated point images of two or more midpoints, and a point image group of separated point images of far points.

[0292] (S55: Execute Zernike polynomial fitting processing according to the point image group)

[0293] Next, the main control unit 111 controls the Zernike polynomial fitting processing unit 133E to perform Zernike polynomial fitting processing according to the point image group determined in step S54, thereby calculating wavefront aberration information (wavefront fitting formula) represented by Zernike coefficients and Zernike polynomials according to the point image group. The Zernike polynomial fitting processing unit 133E uses the pupil diameter information acquired in step S2 to normalize the wavefront aberration information calculated according to the point image group.

[0294] (S56: Calculate the diopter according to the point image group (SCA))

[0295] Next, the main control unit 111 controls the third refractive power calculation unit 133 to calculate the spherical power S, the astigmatism power C and the astigmatism axis angle A according to the point image group through known operations based on the Zernike coefficients obtained by the Zernike polynomial fitting processing performed according to the point image group in step S55.

[0296] above, Fig.17 The third refractive power calculation process in step S26 ends (END).

[0297] exist Fig.17 In step S28, the fourth diopter calculation unit 134 calculates Fig.21 The illustrated flow executes the fourth diopter calculation process.

[0298] (S61: Determine point image)

[0299] exist Fig.17 In step S28, first, the main control unit 111 controls the point image determination unit 134A to determine the point images constituting the Hartmann image acquired in step S10. In some embodiments, the main control unit 111 controls the fourth refractive power calculation unit 134 to control the point image determination unit 134A as described above after performing point image enhancement processing on the Hartmann image acquired in step S10.

[0300] (S62: Is it configured in each area?)

[0301] Next, the main control unit 111 determines whether the plurality of point images determined in step S61 are as follows: Fig.10 or Fig.11 In some embodiments, the main control unit 111 controls the fourth refractive power calculation unit 134 to determine the representative position of the point image determined in step S61 in the same manner as step S42, and determines whether the point image is configured in each area corresponding to the focal length of the IOL in the same manner as step S43 based on the determined representative position.

[0302] When it is determined that the determined plurality of point images are arranged in each area corresponding to the focal length of the IOL (S62: Yes), the fourth refractive power calculation process is transferred to step S63. When it is determined that the determined plurality of point images are not arranged in each area corresponding to the focal length of the IOL (S62: No), the fourth refractive power calculation process is transferred to step S64.

[0303] (S63: Second diopter calculation process)

[0304] In step S62, when it is determined that the determined plurality of point images are arranged in each area corresponding to the focal length of the IOL (S62: YES), the main control unit 111 controls the second refractive power calculation unit 132 to execute a second refractive power calculation process in which the refractive power of the eye E to be inspected is calculated based on the point images determined in step S61. Fig.19 The flow shown executes the second diopter calculation process. Fig.17 The processing of step S28 ends (END).

[0305] (S64: Are the point images separated?)

[0306] In step S62, when the determined plurality of point images are not arranged in each area corresponding to the focal length of the IOL (S62: No), the main control unit 111 determines whether the plurality of point images that constitute the Hartmann image determined in step S61 are point images that are greater than a predetermined threshold value. Fig.13 As shown, it is separated into two or more separate points.

[0307] When it is determined that the point images of the plurality of point images determined are separated into two or more separated point images (S64: Yes), the fourth refractive power calculation process is transferred to step S65. When it is determined that the point images of the plurality of point images determined are separated into two or more separated point images (S64: No), the fourth refractive power calculation process is transferred to step S66.

[0308] (S65: Third diopter calculation process)

[0309] In step S64, when it is determined that the point images of the plurality of point images determined by the predetermined threshold value or more are separated into two or more separated point images (S64: Yes), the main control unit 111 controls the third refractive power calculation unit 133 to execute a third refractive power calculation process in which the refractive power of the subject's eye E is calculated based on the point images determined in step S61. The third refractive power calculation unit 133 calculates the refractive power of the subject's eye E based on the point images determined in step S61. Fig. 20 The flow shown executes the third diopter calculation process. Fig.17The processing of step S28 ends (END).

[0310] (S66: Ellipse Fitting Process)

[0311] In step S64, when it is determined that the point images above the predetermined threshold value among the determined multiple point images are not separated into two or more separated point images (S64: No), the main control unit 111 controls the ellipse fitting processing unit 134B to perform a known ellipse fitting process on each of the multiple point images determined in step S61. The ellipse fitting processing unit 134B determines multiple fitting ellipses for each of the multiple point images determined in step S61, and determines two foci of each of the determined multiple fitting ellipses.

[0312] (S67: Determine point image group)

[0313] Next, the main control unit 111 controls the point image group determination unit 134C to determine the focus close to the center of the Hartmann image among the two foci of the fitting ellipse determined in step S66 as the near point image, and to determine the focus far from the center of the Hartmann image as the far point image. The point image group determination unit 134C classifies the plurality of near point images and the plurality of far point images determined for the plurality of fitting ellipses into a point image group of near point images and a point image group of far point images.

[0314] (S68: Execute Zernike polynomial fitting process according to point image group)

[0315] Next, the main control unit 111 controls the Zernike polynomial fitting processing unit 134D to perform Zernike polynomial fitting processing according to the point image group determined in step S67, thereby calculating wavefront aberration information (wavefront fitting formula) represented by Zernike coefficients and Zernike polynomials according to the point image group. The Zernike polynomial fitting processing unit 134D uses the pupil diameter information acquired in step S2 to normalize the wavefront aberration information calculated according to the point image group.

[0316] (S69: Calculation of diopter according to point image group (SCA))

[0317] Next, the main control unit 111 controls the fourth refractive power calculation unit 134 to calculate the spherical power S, the astigmatism power C and the astigmatism axis angle A according to the point image group through known operations based on the Zernike coefficients obtained by the Zernike polynomial fitting processing performed according to the point image group in step S68.

[0318] Above, the end Fig.17 The fourth diopter calculation process in step S28 (END).

[0319] exist Fig.16 In step S12, for example, the main control unit 111 can cause the display unit 170 to display the following information.

[0320] Fig. 22 Show Fig.16 The first display example is an example of a display of the calculation result of the diopter.

[0321] The main control unit 111 controls the diopter calculation unit 130 to calculate the diopter value according to the Fig.16 The spherical equivalent (SE) is calculated by a known calculation method based on the refractive power (SCA) calculated in step S11. Thus, except for the monofocal IOL, the refractive power (spherical power (S), cylindrical power (C), astigmatism axis angle (A), and spherical equivalent (SE)) is calculated according to the focal length of the IOL according to the type of IOL. The main control unit 111 causes the display unit 170 to display the calculated refractive power.

[0322] The diopter calculation unit 130 can calculate the difference between the far point and the near point for the spherical power (S), the cylindrical power (C), the astigmatism axis angle (A), and the spherical equivalent power (SE).

[0323] For example, the main control unit 111 causes the display unit 170 to display the refractive power (i) of the far point and the near point of the refractive power calculated according to the focal length (region) of the IOL according to the type of the IOL. Fig. 22 ).

[0324] Fig.23 Show Fig.16 The second display example of the display unit 170 in step S12 is shown in FIG.

[0325] The main control unit 111 controls the distribution information generating unit 140 to generate distribution information (wavefront aberration map) indicating the distribution of wavefront aberration according to the focal length of the IOL. The main control unit 111 causes the display unit 170 to display the generated distribution information.

[0326] The main control unit 111 generates the distribution information of the far point and the near point among the distribution information that can be generated according to the focal length of the IOL, and can cause the display unit 170 to display the generated distribution information of the outer point group (far point group) and the inner point group (near point group). Fig.23 ).

[0327] Fig.24 Show Fig.16 The third display example is a display example of the simulation result.

[0328] The main control unit 111 controls the simulation processing unit 150 to execute the vision simulation, and causes the display unit 170 to display the generated simulation result. The simulation processing unit 150 obtains a plurality of vision values ​​of the subject's eye E corresponding to a plurality of object points while changing the positions of the object points.

[0329] The main control unit 111 superimposes the characteristic information (product specification) T1 of the IOL determined based on the IOL information, and displays the visual acuity simulation result T2 on the display unit 170 ( Fig.24 ).

[0330] Fig.25 Show Fig.16 The fourth display example is a display example of a simulated image showing a visual state of an optotype.

[0331] The main control unit 111 controls the simulation processing unit 150 to obtain the PSF according to the multiple focal lengths of the IOL or one or more predetermined fixed distances, and calculates the convolution integral (convolution) of the obtained PSF and the image data (brightness distribution) of the visual mark, thereby generating a simulated image when the visual mark is projected onto the fundus Ef.

[0332] exist Fig.25 The images corresponding to the sight marks at fixed distances include an image of a landscape corresponding to a sight mark at infinity, an image of a desktop computer screen corresponding to a sight mark at 1 m, an image of a notebook computer screen corresponding to a sight mark at 40 cm, and an image of a smartphone screen corresponding to a sight mark at 20 cm. The simulation processing unit 150 calculates Fig.25 The main control unit 111 causes the display unit 170 to display a simulated image showing the visual state of the sight mark at a fixed distance of infinity, 1m, 40cm, and 20cm. Fig.25 In the example, the sight mark can also be a blue ring.

[0333] As described above, according to the first embodiment, based on the wavefront aberration information obtained in a state where the IOL is focused on the eye E corresponding to the average focal length of the IOL, the refractive power of the eye E wearing the IOL is calculated by a calculation processing method corresponding to the type of IOL worn by the eye E, thereby improving the reliability of the calculation result of the refractive power of the eye E wearing the IOL.

[0334] <Second Embodiment>

[0335] Generally, it is believed that the eye to be examined wearing an IOL loses the accommodation function. However, the eye to be examined wearing an IOL can be given the accommodation function by the movement of the ciliary body, etc. Therefore, in the second embodiment, the wavefront aberration is measured at two or more distances including the far point side and the near point side, and the far diopter (the diopter of the far point) and the near diopter (the diopter of the near point) are calculated at each position.

[0336] Hereinafter, the configuration and operation of the ophthalmologic apparatus of the second embodiment will be described focusing on the features different from the ophthalmologic apparatus 100 of the first embodiment.

[0337] The structure of the ophthalmologic apparatus of the second embodiment is the same as the structure of the ophthalmologic apparatus 100 of the first embodiment.

[0338] Fig.26 and Fig. 27 A flowchart showing an operation example of the ophthalmologic apparatus according to the second embodiment. Fig.26 and Fig. 27 The flowchart shows an operation example of the ophthalmologic apparatus for calculating the refractive power of the subject's eye E by a calculation processing method according to the type of IOL worn by the subject's eye E. The storage unit 112 stores the data for realizing Fig.26 and Fig. 27 The main control unit 111 operates according to the computer program, thereby executing Fig.26 and Fig. 27 Processing shown.

[0339] (S71: Obtaining IOL Information)

[0340] First, the main control unit 111 acquires the IOL information worn by the eye to be inspected E in the same manner as in step S1 .

[0341] (S72: Obtaining pupil diameter information)

[0342] Next, the main control unit 111 acquires pupil diameter information indicating the pupil diameter of the eye to be inspected E in the same manner as in step S2 .

[0343] (S73: Alignment)

[0344] Next, the main control unit 111 performs alignment while presenting a fixation target to the eye E to be inspected, similarly to step S3 .

[0345] After the alignment is completed, the main control unit 111 moves the moving unit 69 (light source 61), the moving unit 77, and the moving unit 46 to the position of the origin (e.g., the position equivalent to 0D) along the optical axis. In some embodiments, the main control unit 111 moves the moving unit 69 (light source 61), the moving unit 77, and the moving unit 46 to the position of the origin (e.g., the position equivalent to 0D) along the optical axis before performing the alignment.

[0346] (S74: Is it a multifocal diffractive IOL?)

[0347] Next, the main control unit 111 determines whether the IOL worn by the eye to be inspected E is a multifocal diffractive IOL based on the IOL information acquired in step S71 , similarly to step S8 .

[0348] In step S74, when it is determined that the IOL worn by the subject's eye E is a multifocal diffractive IOL (S74: Yes), the operation of the ophthalmologic apparatus proceeds to step S75. In step S74, when it is determined that the IOL worn by the subject's eye E is not a multifocal diffractive IOL (S74: No), the operation of the ophthalmologic apparatus proceeds to step S76.

[0349] (S75: Switching light source)

[0350] In step S74 , when it is determined that the IOL worn by the subject's eye E is a multifocal diffractive IOL ( S74 : YES), the main control unit 111 controls the light source 61 in the same manner as in step S9 , and switches the measurement light source from the light source 61B to the light source 61A.

[0351] (S76: Obtain Hartmann Image)

[0352] After step S75 or in step S74 , when it is determined that the IOL worn by the subject's eye E is not a multifocal diffractive IOL ( S74 : No), the main control unit 111 performs preliminary measurement in the same manner as in step S4 .

[0353] (S77: Calculate diopter)

[0354] Next, the main control unit 111 causes the diopter calculation unit 130 to calculate the diopter based on the intervals between the point images constituting the Hartmann image detected by the area sensor 76, similarly to step S5, and determines the movement amount of the moving unit 77 including the collimating lens 74 as the focus lens based on the calculated diopter.

[0355] (S78: Move the focus lens (for telephoto))

[0356] The main control unit 111 moves the moving unit 77 (collimating lens 74 as a focus lens) along the optical axis to a position corresponding to the far point according to the movement amount corresponding to the diopter (spherical power S) calculated in step S77, similarly to step S6. In conjunction with this, the moving unit 46 and the moving unit 69 also move along the optical axis direction by the movement amount corresponding to the diopter.

[0357] (S79: Is this your first time?)

[0358] Next, the main control unit 111 determines whether the movement of the moving unit 77 and the like based on the preliminary measurement is the first time, similarly to step S7 .

[0359] When it is determined that the movement is the first time (S79: Yes), the operation of the ophthalmologic apparatus proceeds to step S76. When it is determined that the movement is not the first time (S79: No), the operation of the ophthalmologic apparatus proceeds to step S80.

[0360] (S80: Obtaining Hartmann Image)

[0361] In step S79, when it is determined that the movement is not the first time (S79: No), the main control unit 111 moves the moving unit 46 further by a predetermined diopter along the optical axis direction from the position corresponding to the far point moved in step S78, so that the subject's eye E observes the sight mark in a foggy state. In addition, it may be determined that the subject's eye wearing the IOL does not have accommodation power, and the foggy vision function is omitted.

[0362] The main control unit 111 irradiates the subject's eye E with light (near infrared light or visible light) from the light source 61 (light source 61A or light source 61B) as a formal measurement, and detects a Hartmann image (point image group) based on the return light from the subject's eye E through the area sensor 76 .

[0363] (S81: Is it a multifocal IOL?)

[0364] Next, the main control unit 111 determines whether the IOL worn by the eye to be inspected E is a multifocal IOL based on the IOL information acquired in step S71 .

[0365] When it is determined that the IOL worn by the subject's eye E is a multifocal IOL (S81: Yes), the operation of the ophthalmologic apparatus proceeds to step S82. When it is determined that the IOL worn by the subject's eye E is not a multifocal IOL (S81: No), the operation of the ophthalmologic apparatus proceeds to step S84.

[0366] (S82: Move the focus lens (for close use))

[0367] In step S81, when it is determined that the IOL worn by the subject's eye E is a multifocal IOL (S81: Yes), the main control unit 111 moves the moving unit 77 (the collimating lens 74 as a focusing lens) along the optical axis to the near position. In conjunction with this, the moving unit 46 and the moving unit 69 also move along the optical axis by an amount corresponding to the diopter. The near position includes, for example, a fixed position such as 40 cm, a position frequently used by the subject's eye E, and a near position predetermined corresponding to the IOL worn by the subject's eye E.

[0368] (S83: Obtaining Hartmann Image)

[0369] Next, the main control unit 111 irradiates the subject's eye E with light (near infrared light or visible light) from the light source 61 (light source 61A or light source 61B) as a formal measurement, and detects the Hartmann image (point image group) based on the return light from the subject's eye E using the area sensor 76.

[0370] (S84: Calculation of diopter)

[0371] After step S83 or in step S81, when it is determined that the IOL worn by the subject's eye E is not a focal IOL (S81: No), the main control unit 111 causes the diopter calculation unit 130 to calculate the diopter based on the interval of the point images constituting the Hartmann image detected by the area sensor 76 in step S83 or step S76, as in step S11. The diopter calculation unit 130 calculates the diopter of the subject's eye E by a calculation processing method corresponding to the IOL information acquired in step S71, as in step S11, and therefore detailed description of step S84 is omitted.

[0372] (S85: Output)

[0373] Next, the main control unit 111 causes the display unit 170 to display the diopter calculated in step S84, similarly to step S12. In some embodiments, the main control unit 111 controls the distribution information generating unit 140 to cause the display unit 170 to display the generated distribution information. In some embodiments, the main control unit 111 controls the simulation processing unit 150 to cause the display unit 170 to display the acquired simulation result. In some embodiments, the main control unit 111 causes the display unit 170 to display the measurement result obtained by the wavefront aberration measurement in association with the simulation result.

[0374] With the above, the operation of the ophthalmologic apparatus according to the second embodiment ends (END).

[0375] For example, the distance diopter and the near diopter can be obtained from the Hartmann image obtained by the distance measurement in step S76, and the distance diopter and the near diopter can be obtained from the Hartmann image obtained by the near measurement in step S83. At this time, the ophthalmic apparatus can also selectively output the distance diopter obtained by the distance measurement and the near diopter obtained by the near measurement.

[0376] In addition, Fig.26 and Fig. 27 In the embodiment 1, the case where the number of focal points of the IOL is "1" (single focus type) or "2" is described, but the second embodiment is not limited to this. For example, when the number of focal points is three or more, steps S82 to S83 can be repeated to obtain Hartmann images of the number of focal points, and the refractive power of the number of focal points can be calculated according to the obtained Hartmann images.

[0377] As described above, according to the second embodiment, a plurality of Hartmann images are obtained in a state where the subject's eye E is focused corresponding to a plurality of focal lengths possessed by the IOL, and the refractive power is calculated using each Hartmann image. Therefore, even when the subject's eye wearing the IOL has an accommodation function, the reliability of the calculation result of the refractive power of the subject's eye wearing the IOL can be improved.

[0378] [effect]

[0379] An ophthalmologic information processing device, an ophthalmologic device, an ophthalmologic information processing method, and a program according to an embodiment will be described.

[0380] The first mode of several embodiments is an ophthalmic information processing device (calculation processing unit 120) that calculates the diopter of the eye to be inspected based on wavefront aberration information obtained by measuring the wavefront aberration of the eye to be inspected (E) wearing an intraocular lens. The ophthalmic information processing device includes an acquisition unit (communication unit 190 or aberration measurement projection system 6 and aberration measurement light receiving system 7) and a calculation unit (diopter calculation unit 130). The acquisition unit acquires at least intraocular lens information representing the optical characteristics of the intraocular lens. The calculation unit changes the calculation processing method of the diopter in response to the intraocular lens information and calculates the diopter of the eye to be inspected.

[0381] According to this aspect, the refractive power of the subject's eye wearing the IOL is calculated by a calculation processing method according to the type of IOL worn by the subject's eye, so the reliability of the calculation result of the refractive power of the subject's eye wearing the IOL can be improved.

[0382] In the ophthalmologic information processing apparatus of a second aspect of some embodiments, in the first aspect, the acquisition unit acquires pupil diameter information indicating a pupil diameter, and the calculation unit calculates the diopter based on the wavefront aberration information in a region defined based on the pupil diameter information.

[0383] According to such an aspect, the diopter is calculated based on the wavefront aberration information corresponding to the pupil diameter, and therefore the reliability of the calculation result of the diopter of the eye to be inspected wearing the IOL can be further improved.

[0384] In the ophthalmologic information processing apparatus of a third aspect of some embodiments, the wavefront aberration information includes a Hartmann image obtained in a state where the eye to be inspected is in focus corresponding to an average focal length of the intraocular lens.

[0385] According to such a mode, the reliability of the calculation result of the refractive power of the eye to be inspected wearing the IOL can be improved through simple control according to the type of the IOL.

[0386] In an ophthalmologic information processing apparatus according to a fourth aspect of some embodiments, in the first aspect, the wavefront aberration information includes a plurality of Hartmann images obtained in a state where the eye to be inspected is focused corresponding to a plurality of focal lengths of the intraocular lens, respectively.

[0387] In this way, multiple Hartmann images are obtained in a state where the eye to be inspected is focused corresponding to the multiple focal lengths of the IOL, and the refractive power is calculated using each Hartmann image. Therefore, even if the eye to be inspected wearing the IOL has an accommodation function, the reliability of the calculation result of the refractive power of the eye to be inspected wearing the IOL can be improved.

[0388] In an ophthalmologic information processing apparatus according to a fifth aspect of some embodiments, in any one of the first to fourth aspects, the intraocular lens information indicates either a monofocal type or a multifocal type.

[0389] According to such an aspect, the reliability of the calculation result of the refractive power of the eye to be inspected wearing the monofocal IOL or the multifocal IOL can be improved.

[0390] In an ophthalmologic information processing apparatus according to a sixth aspect of some embodiments, in the fifth aspect, when the intraocular lens is a monofocal intraocular lens, the calculation unit calculates a single refractive power based on the wavefront aberration information.

[0391] According to such an aspect, according to the types of the plurality of IOLs including the monofocal type IOL, the calculation result of the refractive power of the eye to be inspected wearing the IOL can be improved.

[0392] In an ophthalmic information processing apparatus according to a seventh aspect of some embodiments, in the fifth aspect, when the intraocular lens is a multifocal intraocular lens, the calculation unit calculates a plurality of diopters corresponding to a plurality of focal lengths of the intraocular lens based on the wavefront aberration information.

[0393] According to such an aspect, the calculation result of the refractive power of the eye to be inspected wearing the IOL can be improved according to the types of the plurality of IOLs including the multifocal IOL.

[0394] In an ophthalmologic information processing apparatus according to an eighth aspect of some embodiments, in the fifth aspect, the multifocal type includes a multifocal refractive type and a multifocal diffractive type.

[0395] According to such a mode, according to the types of the plurality of IOLs including the multifocal refractive IOL and the multifocal diffractive IOL, the calculation result of the refractive power of the eye to be inspected wearing the IOL can be improved.

[0396] In an ophthalmic information processing apparatus of a ninth aspect of some embodiments, in the eighth aspect, when the intraocular lens is a multifocal refractive intraocular lens, the calculation unit calculates a plurality of diopters for each region corresponding to the focal length of the intraocular lens based on wavefront aberration information.

[0397] According to such an aspect, since the calculation is performed according to the focal length (area) of the IOL, the reliability of the calculation result of the refractive power of the eye to be inspected wearing the multifocal refractive IOL can be improved.

[0398] In the ophthalmic information processing device of the tenth aspect of several embodiments, in the eighth aspect, the wavefront aberration information includes a Hartmann image. When the intraocular lens is a multifocal diffractive intraocular lens, the calculation unit classifies two or more separated point images separated from the point image constituting the Hartmann image according to the focal length, and calculates a plurality of diopters according to the focal length based on the classified two or more separated point images.

[0399] In this way, two or more separated point images separated from the point image constituting the Hartmann image are classified according to the focal length, and multiple refractive powers are calculated according to the focal length based on the classified two or more separated point images, thereby improving the reliability of the calculation results of the refractive power of the eye to be examined wearing a multifocal diffractive IOL.

[0400] In the ophthalmic information processing device of the eleventh mode of several embodiments, in the eighth mode, the multifocal type further includes an extended depth of field type. The wavefront aberration information includes a Hartmann image. When the intraocular lens is an extended depth of field type intraocular lens, the calculation unit classifies two foci of a fitting ellipse determined by performing ellipse fitting on a plurality of point images constituting the Hartmann image, according to the focal length, and calculates a plurality of diopters according to the focal length based on the classified two or more separated point images.

[0401] In this way, the two foci of the fitted ellipse determined by performing ellipse fitting on multiple point images constituting the Hartmann image are classified according to the focal length, and multiple refractive powers are calculated according to the focal length based on the classified two or more separated point images, thereby improving the reliability of the calculation results of the refractive power of the eye to be examined wearing an EDoF type IOL.

[0402] In the ophthalmic information processing device of the twelfth mode of several embodiments, in the fifth mode, it includes a display control unit (control unit 110, main control unit 111), which causes the display unit (display unit 170) to display the refractive power calculated by the calculation unit for the far point and the near point respectively.

[0403] According to such an aspect, it is possible to cause the display unit to display a highly reliable calculation result of the refractive power of the eye to be inspected wearing the IOL.

[0404] In the ophthalmic information processing device of the thirteenth mode among several embodiments, in the fifth mode, it includes a display control unit (control unit 110, main control unit 111), which causes the display unit (display unit 170) to display an image representing the visual state of the eye to be inspected corresponding to the refractive power calculated by the calculation unit according to the focal length of the intraocular lens or one or more fixed distances.

[0405] According to such an aspect, the display unit can be caused to display an image showing the visual state of the eye to be inspected corresponding to the refractive power calculated according to the type of the IOL, in accordance with the focal length of the IOL or one or more fixed distances.

[0406] In the ophthalmic information processing device of the fourteenth mode among several embodiments, in the fifth mode, it includes a display control unit (control unit 110, main control unit 111), which causes the display unit (display unit 170) to display the simulated result of the visual acuity value of the eye to be examined according to the focal length of the intraocular lens or one or more fixed distances.

[0407] According to such an aspect, the simulation result of the visual acuity value of the subject's eye is displayed according to the focal length of the IOL or one or more fixed distances, and can be easily compared with the refractive power calculated according to the type of IOL.

[0408] The fifteenth mode of several embodiments is an ophthalmic device (100), comprising: a measuring optical system (aberration measurement projection system 6 and aberration measurement light receiving system 7), including a focusing lens (74), for measuring the wavefront aberration of the eye to be examined; and an ophthalmic information processing device of any one of the first to fourth modes.

[0409] According to such a method, an ophthalmologic apparatus can be provided which calculates the refractive power of the subject's eye wearing the IOL by a calculation processing method corresponding to the type of IOL worn by the subject's eye, thereby improving the reliability of the calculation result of the refractive power of the subject's eye wearing the IOL.

[0410] An ophthalmic information processing method according to a sixteenth aspect of several embodiments is an ophthalmic information processing method in which the refractive power of the subject's eye is calculated based on wavefront aberration information obtained by measuring the wavefront aberration of the subject's eye (E) wearing an intraocular lens. The ophthalmic information processing method includes: an acquisition step of acquiring at least intraocular lens information indicating the optical characteristics of the intraocular lens; and a calculation step of changing a calculation processing method of the refractive power in response to the intraocular lens information, and calculating the refractive power of the subject's eye.

[0411] According to this aspect, the refractive power of the subject's eye wearing the IOL is calculated by a calculation processing method according to the type of IOL worn by the subject's eye, so the reliability of the calculation result of the refractive power of the subject's eye wearing the IOL can be improved.

[0412] In the ophthalmic information processing method of the seventeenth mode among several embodiments, in the sixteenth mode, the acquisition step acquires pupil diameter information indicating the pupil diameter, and in the calculation step, the refractive power is calculated based on the wavefront aberration information within the area defined based on the pupil diameter information.

[0413] According to such an aspect, the diopter is calculated based on the wavefront aberration information corresponding to the pupil diameter, and therefore the reliability of the calculation result of the diopter of the eye to be inspected wearing the IOL can be further improved.

[0414] In an ophthalmologic information processing method according to an eighteenth aspect of some embodiments, in the sixteenth aspect, the wavefront aberration information includes a Hartmann image obtained in a state where the eye to be inspected is in focus corresponding to an average focal length of the intraocular lens.

[0415] According to such a mode, the reliability of the calculation result of the refractive power of the eye to be inspected wearing the IOL can be improved through simple control according to the type of the IOL.

[0416] In a nineteenth aspect of some embodiments, in the sixteenth aspect, the wavefront aberration information includes a plurality of Hartmann images obtained in a state where the eye to be inspected is focused corresponding to a plurality of focal lengths of the intraocular lens, respectively.

[0417] In this way, multiple Hartmann images are obtained in a state where the eye to be inspected is focused corresponding to the multiple focal lengths of the IOL, and the refractive power is calculated using each Hartmann image. Therefore, even if the eye to be inspected wearing the IOL has an accommodation function, the reliability of the calculation result of the refractive power of the eye to be inspected wearing the IOL can be improved.

[0418] In the ophthalmologic information processing method of a twentieth aspect of some embodiments, in any one of the sixteenth to nineteenth aspects, the intraocular lens information indicates either a monofocal type or a multifocal type.

[0419] According to such an aspect, the reliability of the calculation result of the refractive power of the eye to be inspected wearing the monofocal IOL or the multifocal IOL can be improved.

[0420] In the ophthalmologic information processing method according to a twenty-first aspect of some embodiments, in the twentieth aspect, when the intraocular lens is a monofocal intraocular lens, in the calculation step, a single diopter is calculated based on wavefront aberration information.

[0421] According to such an aspect, according to the types of the plurality of IOLs including the monofocal type IOL, the calculation result of the refractive power of the eye to be inspected wearing the IOL can be improved.

[0422] In the ophthalmic information processing method of the twenty-second aspect of some embodiments, when the intraocular lens is a multifocal intraocular lens, in the calculation step, a plurality of diopters respectively corresponding to a plurality of focal lengths of the intraocular lens are calculated based on the wavefront aberration information.

[0423] According to such an aspect, the calculation result of the refractive power of the eye to be inspected wearing the IOL can be improved according to the types of the plurality of IOLs including the multifocal IOL.

[0424] A program according to a twenty-third aspect of some embodiments is a program that causes a computer to execute each step of the ophthalmologic information processing method according to any one of the sixteenth aspect to the nineteenth aspect.

[0425] According to such a method, a program can be provided that calculates the refractive power of the subject's eye wearing the IOL by a calculation processing method corresponding to the type of IOL worn by the subject's eye, thereby improving the reliability of the calculation results of the refractive power of the subject's eye wearing the IOL.

[0426] (Other Modifications)

[0427] The embodiment described above is merely an example for implementing the present invention, and those who wish to implement the present invention can make any modifications, omissions, additions, etc. within the scope of the gist of the present invention.

[0428] The invention of the above-described embodiment can be applied to a device having any function that can be used in the field of ophthalmology, such as an intraocular pressure measurement function, a fundus imaging function, an anterior ocular imaging function, an optical coherence tomography (OCT) function, and an ultrasonic examination function. In addition, the intraocular pressure measurement function is implemented by a tonometer, etc. The fundus imaging function is implemented by a fundus camera, a scanning ophthalmoscope (SLO), etc. The anterior ocular imaging function is implemented by a slit lamp, etc. The OCT function is implemented by an optical coherence tomography apparatus, etc. The ultrasonic examination function is implemented by an ultrasonic diagnostic apparatus, etc. In addition, the present invention can also be applied to a device (compound machine) having two or more of these functions.

[0429] Description of Reference Numerals

[0430] 4: Visual mark projection system

[0431] 5: Observation system

[0432] 6: Aberration measurement projection system

[0433] 7: Aberration measurement light receiving system

[0434] 61, 61A, 61B: Light source

[0435] 75: Hartmann Plate

[0436] 76: Area Sensor

[0437] 100: Ophthalmic devices

[0438] 110: Control Department

[0439] 111: Main control unit

[0440] 120: Operation processing unit

[0441] 130: Diopter calculation unit

[0442] 131: First diopter calculation unit

[0443] 131A, 132A, 133B, 134A: point image determination unit

[0444] 131B, 132B, 133C: representative position determination unit

[0445] 131C, 132D, 133E, 134D: Zernike polynomial fitting processing unit

[0446] 132: Second diopter calculation unit

[0447] 132C, 133D, 134C: Point image group determination unit

[0448] 133: Third diopter calculation unit

[0449] 133A: Enhanced Processing Unit

[0450] 134: Fourth diopter calculation unit

[0451] 134B: Ellipse fitting processing unit

[0452] 140: Distribution information generation unit

[0453] 150: Analog processing unit

[0454] E: Eye to be examined

[0455] Ef: Fundus

Claims

1. An ophthalmologic information processing device for calculating the refractive power of an eye to be inspected based on wavefront aberration information obtained by measuring the wavefront aberration of an eye to be inspected wearing an intraocular lens, The ophthalmic information processing device comprises: an acquisition unit that acquires at least intraocular lens information indicating optical characteristics of the intraocular lens; as well as The calculation unit calculates the refractive power of the eye to be inspected by changing a calculation processing method of the refractive power in response to the intraocular lens information.

2. The ophthalmologic information processing device according to claim 1, characterized in that: The acquisition unit acquires pupil diameter information indicating pupil diameter, The calculation unit calculates the refractive power based on wavefront aberration information within a region defined based on the pupil diameter information.

3. The ophthalmologic information processing device according to claim 1, characterized in that: The wavefront aberration information includes a Hartmann image obtained in a state where the eye to be inspected is in focus corresponding to the average focal length of the intraocular lens.

4. The ophthalmologic information processing device according to claim 1, characterized in that: The wavefront aberration information includes a plurality of Hartmann images obtained in a state where the eye to be inspected is focused corresponding to a plurality of focal lengths of the intraocular lens, respectively.

5. The ophthalmologic information processing device according to any one of claims 1 to 4, characterized in that: The intraocular lens information indicates either a monofocal type or a multifocal type.

6. The ophthalmologic information processing device according to claim 5, characterized in that: When the intraocular lens is a monofocal intraocular lens, the calculation section calculates a single diopter based on the wavefront aberration information.

7. The ophthalmologic information processing device according to claim 5, characterized in that: When the intraocular lens is a multifocal intraocular lens, the calculation unit calculates a plurality of diopters respectively corresponding to a plurality of focal lengths of the intraocular lens based on the wavefront aberration information.

8. The ophthalmologic information processing device according to claim 5, characterized in that: The multifocal type includes a multifocal refractive type and a multifocal diffractive type.

9. The ophthalmologic information processing device according to claim 8, characterized in that: When the intraocular lens is the multifocal refractive intraocular lens, the calculation unit calculates a plurality of diopters for each region corresponding to the focal length of the intraocular lens based on the wavefront aberration information.

10. The ophthalmologic information processing device according to claim 8, characterized in that: The wavefront aberration information includes Hartmann image, When the intraocular lens is the multifocal diffractive intraocular lens, the calculation unit classifies two or more separated point images separated from the point image constituting the Hartmann image according to focal length, and calculates a plurality of diopters according to focal length based on the classified two or more separated point images.

11. The ophthalmologic information processing device according to claim 8, characterized in that: The multi-focal type also includes a depth-of-field extension type, The wavefront aberration information includes Hartmann image, When the intraocular lens is the intraocular lens of the extended depth of field type, the calculation unit classifies two foci of a fitted ellipse determined by performing ellipse fitting on a plurality of point images constituting the Hartmann image, according to focal length, and calculates a plurality of diopters according to focal length based on the classified two or more separate point images.

12. The ophthalmologic information processing device according to claim 5, characterized in that: The ophthalmic information processing device comprises: The display control unit causes the display unit to display the diopter calculated by the calculation unit for each of the far point and the near point.

13. The ophthalmologic information processing device according to claim 5, characterized in that: The ophthalmic information processing device comprises: The display control section causes a display unit to display an image showing a visual state of the eye to be inspected corresponding to the diopter calculated by the calculation section, in accordance with a focal length of the intraocular lens or in accordance with one or more fixed distances.

14. The ophthalmologic information processing device according to claim 5, characterized in that: The ophthalmic information processing device comprises: The display control section causes the display unit to display a simulation result of the visual acuity value of the eye to be inspected according to the focal length of the intraocular lens or according to one or more fixed distances.

15. An ophthalmic device comprising: A measuring optical system includes a focusing lens and measures the wavefront aberration of the eye to be examined; as well as The ophthalmologic information processing device according to any one of claims 1 to 4.

16. An ophthalmologic information processing method, comprising: calculating the refractive power of a subject's eye based on wavefront aberration information obtained by measuring the wavefront aberration of the subject's eye wearing an intraocular lens, The ophthalmic information processing method comprises: an acquisition step of at least acquiring intraocular lens information representing optical characteristics of the intraocular lens; as well as The calculation step calculates the refractive power of the eye to be inspected by changing the calculation processing method of the refractive power in response to the intraocular lens information.

17. The ophthalmologic information processing method according to claim 16, characterized in that: In the acquisition step, pupil diameter information indicating pupil diameter is acquired, In the calculation step, the refractive power is calculated based on wavefront aberration information within a region defined based on the pupil diameter information.

18. The ophthalmologic information processing method according to claim 16, characterized in that: The wavefront aberration information includes a Hartmann image obtained in a state where the eye to be inspected is focused corresponding to the average focal length of the intraocular lens.

19. The ophthalmologic information processing method according to claim 16, characterized in that: The wavefront aberration information includes a plurality of Hartmann images obtained in a state where the eye to be inspected is focused corresponding to a plurality of focal lengths of the intraocular lens, respectively.

20. The ophthalmologic information processing method according to any one of claims 16 to 19, characterized in that: The intraocular lens information indicates either a monofocal type or a multifocal type.

21. The ophthalmologic information processing method according to claim 20, characterized in that: When the intraocular lens is a monofocal intraocular lens, in the calculation step, a single diopter is calculated based on the wavefront aberration information.

22. The ophthalmologic information processing method according to claim 20, characterized in that: When the intraocular lens is a multifocal intraocular lens, in the calculation step, a plurality of diopters respectively corresponding to a plurality of focal lengths of the intraocular lens are calculated based on the wavefront aberration information.

23. A program, characterized in that The method further comprises causing a computer to execute each step of the ophthalmologic information processing method according to any one of claims 16 to 19.

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