Ophthalmologic device, method for controlling ophthalmologic device, and program

Abstract

An ophthalmic apparatus includes a measurement optical system, an acquisition unit, a control unit, and a calculation unit. The measurement optical system includes a focus lens, and measures wavefront aberration of a subject eye wearing an intraocular lens to acquire a Hartmann image. The acquisition unit acquires at least intraocular lens information indicating optical characteristics of an intraocular lens. The control unit moves the focus lens to a position corresponding to the focal length of the intraocular lens determined on the basis of the intraocular lens information, and acquires a Hartmann image by the measurement optical system. The calculation unit calculates the diopter of the subject eye on the basis of the Hartmann image using a calculation processing method corresponding to the intraocular lens information.

Description

Technical Field

[0001] The present invention relates to an ophthalmic device, a control method and a program for an ophthalmic device. Background Art

[0002] If 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 into the lens capsule. There are various types of IOL. The subject needs to consider the contrast, brightness, distance vision, near vision, etc. of the image and choose the appropriate type of IOL. After the operation, the refractive power of the subject's eye wearing the IOL is measured to confirm the way of seeing, the recovery of vision, etc.

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

[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] Conventional methods calculate the diopter in a uniform manner regardless of the type of IOL. Therefore, there is a problem that the reliability of the diopter calculation result decreases depending on the type of IOL implanted in the examined eye.

[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 a subject's eye wearing an IOL.

[0009] One embodiment is an ophthalmic device, comprising: a measuring optical system, including a focusing lens, which measures the wavefront aberration of an eye under examination wearing an intraocular lens to obtain a Hartmann image; an acquisition unit, which at least obtains intraocular lens information representing the optical characteristics of the intraocular lens; a control unit, which moves the focusing lens to a position corresponding to the focal length of the intraocular lens determined based on the intraocular lens information, and obtains the Hartmann image by the measuring optical system; and a calculation unit, which calculates the refractive power of the eye under examination based on the Hartmann image using an operation processing method corresponding to the intraocular lens information.

[0010] Another embodiment is a method for controlling an ophthalmic device, the ophthalmic device including a measuring optical system, the measuring optical system including a focus lens, and measuring the wavefront aberration of a subject's eye wearing an intraocular lens to acquire a Hartmann image. The method for controlling the ophthalmic device includes: an acquisition step of acquiring at least intraocular lens information indicating the optical characteristics of the intraocular lens; a control step of moving the focus lens to a position corresponding to the focal length of the intraocular lens determined based on the intraocular lens information, and acquiring the Hartmann image through the measuring optical system; and a calculation step of calculating the diopter of the subject's eye based on the Hartmann image using a calculation processing method corresponding to the intraocular lens information.

[0011] Still another aspect of the embodiment is a program that causes a computer to execute each step of the above-mentioned method of controlling an ophthalmologic apparatus.

[0012] According to the present invention, a new technology can be provided for improving the reliability of the calculation result of the refractive power of the subject's eye wearing an IOL. BRIEF DESCRIPTION OF THE DRAWINGS

[0013] Figure 1 It is a schematic diagram showing a configuration example of an optical system of an ophthalmologic apparatus according to an embodiment.

[0014] Figure 2 It is a schematic diagram showing a configuration example of an optical system of an ophthalmologic apparatus according to an embodiment.

[0015] Figure 3 It is a schematic diagram showing a configuration example of an optical system of an ophthalmologic apparatus according to an embodiment.

[0016] Figure 4 It is a schematic diagram showing a configuration example of an optical system of an ophthalmologic apparatus according to an embodiment.

[0017] Figure 5 It is a diagram for explaining the operation of the ophthalmologic apparatus according to the embodiment.

[0018] Figure 6 It is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to an embodiment.

[0019] Figure 7 It is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to an embodiment.

[0020] Figure 8 It is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to an embodiment.

[0021] Fig. 9 It is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to an embodiment.

[0022] Fig.10 It is a schematic diagram for explaining a multifocal refractive IOL according to an embodiment.

[0023] Fig.11 It is a schematic diagram for explaining a multifocal refractive IOL according to an embodiment.

[0024] Fig.12 It is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to an embodiment.

[0025] Fig.13 It is a schematic diagram for explaining a multifocal diffractive IOL according to an embodiment.

[0026] Fig.14 It is a schematic diagram showing a configuration example of a processing system of an ophthalmologic apparatus according to an embodiment.

[0027] Fig.15 It is a schematic diagram for explaining an extended depth of field IOL according to an embodiment.

[0028] Fig.16 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0029] Fig.17 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0030] Fig.18 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0031] Fig.19 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0032] Fig. 20 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0033] Fig.21 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0034] Fig. 22 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0035] Fig.23 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0036] Fig.24 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0037] Fig.25 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0038] Fig.26 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0039] Fig. 27 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0040] Fig.28 This is a flowchart of an operation example of the ophthalmologic apparatus according to the embodiment.

[0041] Fig.29 This is a flowchart of an operation example of the ophthalmologic apparatus according to the first modified example of the embodiment.

[0042] Fig.30 This is a flowchart of an operation example of the ophthalmologic apparatus according to the second modified example of the embodiment. DETAILED DESCRIPTION

[0043] The following describes in detail embodiments of the ophthalmic device, the control method of the ophthalmic device, and the program of the present invention with reference to the accompanying drawings. In addition, the contents of the documents cited in this specification and any known techniques can be incorporated into the following embodiments.

[0044] An ophthalmic device of an embodiment includes a measuring optical system having a focusing lens, and the measuring optical system measures the wavefront aberration of a subject's eye wearing an IOL (intraocular lens) to obtain a Hartmann image. For example, the IOL is implanted in a lens capsule whose contents have been removed by surgery, so that the subject's eye can wear the IOL. The ophthalmic device moves the focusing lens to a position corresponding to the focal length of the IOL determined at least based on IOL information representing the optical characteristics of the IOL, and calculates the refractive power of the subject's eye based on the Hartmann image obtained by the measuring optical system using an operation processing method corresponding to the IOL information. In some embodiments, the ophthalmic device calculates the refractive power based on the Hartmann image within an area delimited by pupil diameter information representing the pupil diameter.

[0045] 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 utilized, information indicating whether the diffraction phenomenon of light is utilized, and at least one of information indicating whether the IOL has a deep focal depth. Such IOL information can be determined according to a predetermined IOL type. IOL types include monofocal type and multifocal type. Multifocal types include multifocal diffractive type and multifocal refractive type. In some embodiments, the multifocal type includes an extended depth of field (Extended Depth of Focus: hereinafter referred to as EDoF) type. Such IOL information is obtained by a user (subject, examiner, doctor, etc.) specifying using an operating unit or by analyzing an anterior ocular image or a transillumination image of the subject's eye to determine the type of IOL implanted in the subject's eye.

[0046] The ophthalmic device changes the driving method of the focus lens and the calculation method of the diopter according to the IOL information, and calculates the diopter corresponding to the IOL type. The wavefront aberration information includes a Hartmann image obtained in a state where the subject's eye is focused corresponding to the focal length (or 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 diopter includes, for example, spherical power (S), cylindrical power (C), and astigmatism axis angle (A). In some embodiments, the ophthalmic device calculates the diopter for each focal length of the IOL.

[0047] In addition, at least one of the plurality of point images constituting the acquired Hartmann image is separated into two or more separated point images according to the type of IOL. The two or more separated point images respectively correspond to the focal lengths of the IOL. Therefore, the ophthalmic apparatus can classify 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 calculate the diopter by a known method of performing Zernike polynomial fitting according to each point image group.

[0048] In some embodiments, the ophthalmic device acquires pupil diameter information indicating the pupil diameter of the eye to be examined, and calculates the diopter based on wavefront aberration information in a region defined according to the acquired pupil diameter information. For example, the ophthalmic device calculates the diopter by normalizing the wavefront aberration information using the pupil diameter information, and performing Zernike polynomial fitting using the normalized wavefront aberration information.

[0049] Thus, since the refractive power can be obtained by changing the measurement method according to the type of the eye to be examined wearing, the reliability of the calculation result of the refractive power of the eye to be examined wearing the IOL can be improved.

[0050] The ophthalmic device of the embodiment realizes the functions of the ophthalmic information processing device of the embodiment. The control method of the ophthalmic device or the ophthalmic information processing method of the embodiment includes one or more steps for realizing the processing performed by the processor (computer) in the ophthalmic device or the ophthalmic information processing device of the embodiment. The program of the embodiment causes the processor to execute each step of the control method of the ophthalmic device or the ophthalmic information processing method of the embodiment. The recording medium (storage medium) of the embodiment is a non-temporary recording medium (storage medium) readable by a computer having recorded (stored) the program of the embodiment.

[0051] In this specification, "processor" refers to circuits such as CPU (Central Processing Unit), GPU (Graphics Processing Unit), ASIC (Application Specific Integrated Circuit), programmable logic device (for example, 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.

[0052] Hereinafter, the case where the ophthalmic device of the embodiment has the function of the ophthalmic information processing device of the embodiment is described. In addition, the IOL type includes a monofocal type, a multifocal type, and an 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 3 or more.

[0053] The ophthalmic device of the embodiment can perform at least one of any subjective examination and any objective measurement. 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. The subjective examination includes subjective refraction measurement such as far vision examination, near vision examination, contrast examination, glare examination, visual field examination, etc. In the objective measurement, light is irradiated to the subject's eye, and information related to the subject's eye is obtained based on the detection result of its return light. Objective measurement includes measurement for obtaining the characteristics of the subject's eye and shooting for obtaining an image of the subject's eye. Objective measurement includes objective refraction measurement, corneal shape measurement, intraocular pressure measurement, fundus photography, tomographic image photography (OCT photography) using optical coherence tomography (OCT) (hereinafter referred to as OCT), measurement using OCT, etc.

[0054] Hereinafter, the ophthalmic apparatus of the embodiment is an apparatus that 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, a corneal shape measurement, etc. as an objective measurement. However, the configuration of the ophthalmic apparatus of the embodiment is not limited thereto.

[0055] [structure]

[0056] The ophthalmic device of the embodiment includes a face support portion fixed to a base and a stand that can move in the front-back, top-bottom, left-right directions relative to the base. A head portion that houses an optical system for inspecting (measuring) an eye to be inspected is provided on the stand. The face support portion and the head portion can be relatively moved by operating an operating portion disposed at a position on the examiner's side. In addition, the ophthalmic device can automatically relatively move the face support portion and the head portion by performing alignment described later.

[0057] (Optical System)

[0058] exist Figure 1 2 shows an example of the structure of the optical system of the ophthalmologic apparatus of the embodiment. The ophthalmologic apparatus 100 of the embodiment 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 as an optical system for inspecting the inspected eye E. In addition, the ophthalmologic apparatus includes a processing unit 9.

[0059] (Processing unit 9)

[0060] The processing unit 9 controls each part of the ophthalmic apparatus. In addition, the processing unit 9 can perform various calculation processes. The processing unit 9 includes a processor. The processing unit 9 realizes the functions of the embodiment by reading and executing a program stored in a storage circuit or a storage device, for example.

[0061] (Observation system 5)

[0062] 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 the following light (for example, infrared light with a central wavelength of 950 nm) passes through the objective lens 51, passes through the dichroic mirror 52, and passes through the opening of the aperture 53. The light that has passed through the opening of the aperture 53 passes through the half mirror 22, passes through 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 performs imaging and signal output 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 ocular image E' is, for example, an infrared dynamic image.

[0063] (Z alignment system 1)

[0064] The Z alignment system 1 irradiates the subject's eye E with light (infrared light) for alignment in 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 onto the light receiving surface of the linear sensor 13. If 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 obtains 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.

[0065] (XY alignment system 2)

[0066] The XY alignment system 2 irradiates the inspected eye E with light (infrared light) for alignment in directions 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, which is arranged in 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 the relay lens 23 and is reflected by the half-reflecting mirror 22. After the light reflected by the half-reflecting mirror 22 is focused at 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 inspected eye E. 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 inspected eye E. 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 .

[0067] like Figure 1 As shown, the processing unit 9 displays the anterior ocular image E' including the bright spot image Br and the alignment mark AL on the display screen 10a. In the case of manual XY alignment, the examiner moves the optical system so as 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 so as to eliminate the displacement of the bright spot image Br relative to the alignment mark AL.

[0068] (Corneal measurement system 3)

[0069] 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 corneal plate 31 is illuminated by the light from the corneal ring light source 32, thereby projecting an 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 calculates the corneal curvature parameter by performing a known operation based on the corneal ring image. A plastic 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.

[0070] (Sight mark projection system 4)

[0071] The optotype projection system 4 presents various optotypes such as fixation optotypes and subjective inspection optotypes to the inspected eye E. The optotype chart 42 receives control from the processing unit 9 and displays a pattern representing the optotype. The light (visible light) output from the light source 41 passes through the optotype chart 42, passes through 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.

[0072] The moving unit 46 including the light source 41 and the optotype 42 can move 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.

[0073] The sight chart 42 can be controlled by the processing unit 9 to display a pattern representing a fixation mark for causing the inspected eye E to fixate. The fixation position can be moved by sequentially changing the display position of the pattern representing the fixation mark in the sight chart 42, thereby guiding the adjustment of the line of sight and the inspected eye. Such a sight chart 42 has an electronic display device such as a liquid crystal panel and EL (electroluminescence), a device (rotating type) that appropriately arranges any one of a plurality of sight marks drawn on a rotating glass plate or the like on the optical axis, and the like. In addition, the sight chart projection system 4 may also include a glare inspection optical system for projecting the aforementioned sight mark and glare onto the inspected eye E together.

[0074] In the case of a subjective examination, the processing unit 9 controls the moving unit 46 based on 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 examinee. The examinee responds to the optotype. The processing unit 9 receives the input of the response content and performs further 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 based on the response to the Landolt ring, etc., and determines the visual acuity value by repeating the above operation.

[0075] In objective measurement (objective refraction measurement, etc.), a landscape image is projected onto the fundus Ef. The subject is asked to fix his / her eyes on the landscape image. Figure 1 Align while measuring the diopter in foggy vision.

[0076] (Aberration measurement projection system 6, aberration measurement light receiving system 7)

[0077] The aberration measurement projection system 6 and the aberration measurement light receiving system 7 are used to measure the eyeball aberration characteristics of the inspected 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 inspected eye E. The eyeball aberration characteristics of the inspected eye E are obtained based on the light reception result of the return light measured by the aberration measurement light receiving system 7.

[0078] The aberration measurement projection system 6 includes a light source 61 that can output light in two or more wavelength regions with different central wavelengths. The light source 61 can be composed of a single light source that can change the wavelength region (central wavelength) of the output light, or can be composed of two or more light sources that can switch between output lights with 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 some embodiments, the light path from the light source 61A and the light path from the light source 61B are coupled by a dichroic mirror, and are controlled so that the light source 61A and the light source 61B are exclusively turned on. In some embodiments, the light path from the light source 61A and the light path from the light source 61B are coupled by 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.

[0079] Light sources (point light sources) 61A and 61B 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 diameters.

[0080] The moving unit 69 including the light source 61 can move 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 passes 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 that has passed 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.

[0081] exist Figure 2 An example of the wavelength selection characteristics of the beam splitter 68 is schematically shown in FIG. Figure 2 In the figure, the vertical axis represents the transmittance of light and the horizontal axis represents the wavelength.

[0082] 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 (560 nm) of light output by the light source 61A, the second wavelength λ2 is the center wavelength (840 nm) of light output by the light source 61B, and the third wavelength λ3 is the center wavelength (950 nm) of light output by the anterior ocular illumination light source 57.

[0083] Thus, the beam splitter 68 transmits the light from the sight mark projection system 4, reflects the light from the light sources 61A and 61B of the aberration measurement projection system 6 and the return light thereof, and can perform good wavelength separation of the aberration measurement projection system 6, the aberration measurement light receiving system 7, and the sight mark projection system 4. Such a beam splitter 68 may be, for example, a wavelength selective reflector as disclosed in Japanese Patent Application Laid-Open No. 2010-099354.

[0084] Alternatively, no light source may be arranged at the position of the light source 61, and 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 ophthalmologic apparatus. In this case, the fiber end of the optical fiber is arranged at a position substantially optically conjugate with the fundus Ef.

[0085] The rotating prism 67 is used to average out unevenness in reflectance of blood vessels or diseased areas of the fundus Ef or to reduce speckle noise caused by the SLD light source.

[0086] The light incident on the eye E to be examined cannot maintain 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. The 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 that has passed 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 reflected positively on the surface of the objective lens 51 or the cornea K of the eye E to be examined maintains s-polarization, it is reflected by the polarization beam splitter 66 and does not enter the aberration measurement light receiving system 7, so the occurrence of ghosting can be reduced.

[0087] 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 subject's eye E. 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 according to the refractive power of the subject's eye E so that the fundus Ef is roughly optically conjugate with the front focus position of the collimating lens 74.

[0088] exist Figure 3 and Figure 4 2 is an explanatory diagram of the 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.

[0089] The Hartmann plate 75 generates a plurality of convergent lights based on 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 condenses each light beam.

[0090] For example, Figure 3 As shown, the Hartmann plate 75 has a structure in which a plurality of micro lenses 75A are arranged on a glass plate by etching, molding, etc. In this case, the opening of each micro lens can be increased, and the signal strength can be improved.

[0091] In addition, if Figure 4 As shown, the structure of the Hartmann plate 75 may be such that a shading portion 75B is provided by forming a chrome shading film or the like around each microlens 75A, and a plurality of microlenses 75A are arranged. The microlenses 75A are not limited to being arranged in a square, but may be arranged on concentric circles, at the vertices of a triangle, or in a hexagonal close arrangement.

[0092] The area sensor 76 is disposed at the focal position of the microlens 75A, and detects the light (convergent light) respectively focused by the Hartmann plate 75. Figure 5 As shown, on the light receiving surface of the area sensor 76, the microlens 75A of the Hartmann plate 75 and the irradiation area a of the light on the pupil Ep of the eye E to be examined are connected. 1 ……b 1……c 1 ...correspondingly forms a point image A 1 ……B 1 ……C 1 ……. As described above, when the fundus Ef and the front focal position of the collimating lens 74 are in a roughly optically conjugate relationship, the interval between the centroid positions of the point images (or the brightness peak positions 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 analyzes the position of the point image formed by each microlens 75A by acquiring 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, thereby obtaining the wavefront aberration of the light incident on the Hartmann plate 75. Thus, the eye aberration characteristics of the subject's eye E are obtained based on the interval between the point images. The processing unit 9 obtains the refractive power of the subject's eye E based on the obtained eye aberration characteristics.

[0093] The processing unit 9 can move the moving unit 69 and the moving unit 77 in the optical axis direction based on the calculated diopter so that the light source 61 (light source 61A, 61B), the fundus Ef and the front focal position of the collimating lens 74 are optically conjugated. Furthermore, the processing unit 9 can move the moving unit 46 in the optical axis direction in conjunction with the movement of the moving units 69 and 77.

[0094] In some embodiments, the ophthalmic device 100 can obtain a transillumination image of the inspected eye E. For example, one (or part) of the plurality of anterior ocular illumination light sources 57 is turned on, so that light is projected from a position away from the optical axis through the pupil to the fundus Ef, and the area sensor 56 receives the return light, thereby obtaining a transillumination image.

[0095] In some embodiments, the XY alignment light source 21 is turned on, and the light is projected through the pupil to the fundus Ef, and the return light is received by the area sensor 56, thereby acquiring 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 an LD serving as an alignment light source during alignment, and light is output from an SLD or a high-brightness LED serving as an illumination light source for transillumination image acquisition during transillumination image acquisition.

[0096] (Structure of processing system)

[0097] The processing system of the ophthalmologic apparatus 100 according to the embodiment will be described.

[0098] Figure 6 A functional configuration example of the processing system of the ophthalmologic apparatus 100 is shown. Figure 6 FIG. 1 is a diagram showing an example of a functional block diagram of a processing system of an ophthalmic apparatus according to an embodiment. Figure 6 In, with Figure 1 The same parts are denoted by the same reference numerals, and the description thereof will be appropriately omitted.

[0099] 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 .

[0100] 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 front-back, top-bottom, left-right 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 gear combination, a rack 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.

[0101] (Control Unit 110)

[0102] 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.

[0103] 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. Thus, the Z alignment light source 11 is switched between lighting and non-lighting, 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 on 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, and controls the moving mechanism 200 based on this to move the head in the front-to-back direction (Z alignment).

[0104] 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 XY alignment light source 21 is switched between lighting and non-lighting, or the light intensity is changed. The main control unit 111 imports the signal detected by the area sensor 56, and determines the bright spot image position based on the return light from the XY alignment light source 21 based on 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 to eliminate the displacement of the bright spot image position relative to the predetermined target position (for example, the center position of the alignment mark) (XY alignment).

[0105] The control of the cornea measurement system 3 includes the control of the cornea ring light source 32. The control of the cornea ring light source 32 includes the lighting, extinguishing, light intensity adjustment, etc. of the light source. 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.

[0106] 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 switching of whether the sight mark or the fixation mark is displayed, the display position of the fixation mark, etc. Thus, the sight mark or the fixation mark is 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 in the optical axis direction. Similar to the moving mechanism 200, an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force are provided in the moving mechanism. The main control unit 111 controls the moving mechanism by sending a control signal to the actuator, thereby moving the moving unit 46 in the optical axis direction. Thus, the position of the moving unit 46 is adjusted so that the sight mark chart 42 is optically conjugated with the fundus Ef.

[0107] The control of the observation system 5 includes the control of the area sensor 56, the control of the anterior ocular illumination light source 57, etc. The control of the area sensor 56 includes the exposure adjustment, gain adjustment, and detection rate adjustment 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 control of the anterior ocular illumination light source 57 includes the lighting, extinguishing, and light intensity adjustment of the light source. In this way, the lighting and non-lighting of the anterior ocular illumination light source 57 are switched, only one or part of the anterior ocular illumination light sources 57 are lit, or the light intensity of each light source is changed.

[0108] 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 in the optical axis direction. As with the moving mechanism 200, an actuator for generating a driving force for moving the moving mechanism and a transmission mechanism for transmitting the driving force are provided in the moving mechanism. The main control unit 111 controls the moving mechanism by sending a control signal to the actuator, so that the moving unit 69 moves in the optical axis direction.

[0109] 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, and the like. The control of the area sensor 76 includes the exposure adjustment, gain adjustment, and detection rate adjustment 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 the calculation processing of the eye aberration characteristics based on the imported signal. For example, the aberration measurement light receiving system 7 includes a moving mechanism that moves the moving unit 77 in the optical axis direction. Similar to the moving mechanism 200, 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. The main control unit 111 controls the moving mechanism by sending a control signal to the actuator, so that the moving unit 77 moves in 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 in the optical axis direction.

[0110] The main control unit 111 can function as a display control unit to cause the display unit 170 to display various information. The information displayed on the display unit 170 includes objective measurement results (aberration measurement results) obtained using the above-mentioned optical system, subjective inspection results, images and information based on these results, and the like. For example, the diopter obtained by the calculation processing unit 120 is displayed on the display unit 170. The main control unit 111 can display this information on the display unit 170 for each region of a plurality of focal lengths possessed by the IOL, or can identify and display a portion of this information. In some embodiments, the main control unit 111 causes the display unit 170 to display a wavefront aberration diagram showing the distribution of wavefront aberrations, a simulated image showing a viewing method, and a visual acuity simulation result.

[0111] In addition, the main control unit 111 performs a process of writing data into the storage unit 112 and a process of reading data from the storage unit 112 .

[0112] (Storage Unit 112)

[0113] 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 under examination, and processing results of the calculation processing unit 120. The information about the eye under examination includes information about the subject such as the patient ID and name, and information about the eye under examination such as identification information of the left eye and the right eye. In addition, the storage unit 112 stores various programs and data for operating the ophthalmologic apparatus.

[0114] (Calculation Processing Unit 120)

[0115] The calculation processing unit 120 includes a processor, and executes the following processing of each part according to a computer program stored in a storage unit (or the storage unit 112 ) not shown.

[0116] exist Figure 7 Shown in Figure 6 A functional block diagram of a structural example of the operation processing unit 120.

[0117] The calculation processing unit 120 includes a diopter calculation unit 130 .

[0118] (Diopter Calculation Unit 130)

[0119] The refractive power calculation section 130 uses various calculation processing methods to obtain the refractive power of the inspected eye E. The refractive power calculation section 130 includes a first refractive power calculation section 131 , a second refractive power calculation section 132 , a third refractive power calculation section 133 , and a fourth refractive power calculation section 134 .

[0120] The first refractive power calculation unit 131 is a monofocal refractive power calculation unit, for example, which performs a monofocal calculation process for calculating the refractive power of the subject's eye E using a calculation process method corresponding to a monofocal IOL. The second refractive power calculation unit 132 is a multifocal refractive power calculation unit, for example, which performs a multifocal refractive calculation process for calculating the refractive power of the subject's eye E using a calculation process method corresponding to a multifocal refractive IOL. The third refractive power calculation unit 133 is a multifocal diffractive power calculation unit, for example, which performs a multifocal diffractive calculation process for calculating the refractive power of the subject's eye E using a calculation process method corresponding to a multifocal diffractive IOL. The fourth refractive power calculation unit 134 is an EDoF refractive power calculation unit, for example, which performs an EDoF calculation process for calculating the refractive power of the subject's eye E using a calculation process method corresponding to an EDoF IOL.

[0121] When the functional blocks 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 have the same functions, they may be shared as appropriate.

[0122] (First Refractive Power Calculation Section 131)

[0123] The first refractive power calculation unit 131 calculates a single refractive power based on wavefront aberration information including the Hartmann image obtained by wavefront aberration measurement.

[0124] exist Figure 8 Shown in Figure 7 1 is a functional block diagram of a configuration example of the first refractive power calculation unit 131 shown in FIG.

[0125] 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.

[0126] 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 images are determined by the point image determination unit 131A, the Hartmann image is subjected to point image enhancement processing.

[0127] 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.

[0128] 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 using the known operation of the obtained light inclination amount. The obtained wavefront fitting formula is represented by Zernike coefficients and Zernike polynomials. The wavefront aberration information is represented by the 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 eye E or the pupil diameter of the model eye, for example, as disclosed in 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 operations. For example, the Zernike polynomial fitting processing unit 131C can calculate the diopter using the method disclosed in Japanese Patent Application Laid-Open No. 2002-209854 or Japanese Patent Application Laid-Open No. 2017-213124.

[0129] (Second Refractive Power Calculation Section 132)

[0130] The second refractive power calculation unit 132 calculates a plurality of refractive powers corresponding to a plurality of focal lengths of the IOL, 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 for each region corresponding to the focal length of the IOL.

[0131] exist Fig. 9 Show Figure 7 1 is a functional block diagram of a configuration example of the second refractive power calculation unit 132 shown in FIG.

[0132] 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.

[0133] 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, the Hartmann image is subjected to point image enhancement processing.

[0134] 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.

[0135] The point image group determination unit 132C classifies two or more separated point images obtained by separating the point image to be formed originally into point image groups for each focal length of the IOL.

[0136] The Zernike polynomial fitting processing unit 132D calculates the refractive power of the eye to be examined E for each point image group determined by the point image group determination unit 132C, similarly to the Zernike polynomial fitting processing unit 131C.

[0137] exist 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 of the 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 in concentric circles. Fig.11 This is a diagram showing point images corresponding to a sector-shaped multifocal refractive IOL in which regions with different focal lengths are arranged below a lens region.

[0138] When the number of focal points of the ring-zone multifocal refractive IOL is "2", for example, a near area that enables the focus to be adjusted at close range and a far area that enables the focus to be adjusted at far range are alternately arranged from the center toward the outside. Fig.10 In the embodiment, from the center toward the outside, there are alternately arranged near area NA1, far area FA1, near area NA2, far area FA2...near area NA4 and far area FA4. When the number of focal points of the ring-band type multifocal refractive IOL is "3", the near area, the middle area that can focus at an intermediate distance between near and far, and the far area are similarly arranged from the center toward the outside. When the number of focal points of the ring-band type multifocal refractive IOL is 4 or more, the near area, two or more middle areas with different intermediate distances, and the far area are similarly arranged from the center toward 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.

[0139] 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 the wavefront aberration information obtained from the specified point image group.

[0140] When the focal number 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 as a whole. 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.

[0141] In this case, the second refractive power calculation unit 132 specifies the point image group included in the area corresponding to the focal length, similarly to the annular type, and calculates the refractive power for each point image group based on the wavefront aberration information obtained from the specified point image group.

[0142] 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 far vision area. In some embodiments, the diopter can be calculated based on the point image group included in more than one intermediate vision area.

[0143] (Third Refractive Power Calculation Unit 133)

[0144] The third refractive power calculation unit 133 calculates a plurality of refractive powers corresponding to a plurality of focal lengths of the IOL, 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 for each 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 for each focal length based on the classified two or more separated point images.

[0145] exist Fig.12 Shown in Figure 7 1 is a functional block diagram of a configuration example of the third refractive power calculation unit 133 shown in FIG.

[0146] 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.

[0147] The enhancement processing unit 133A performs point image enhancement processing on 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.

[0148] 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 in 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.

[0149] 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.

[0150] In some embodiments, in order to easily determine the separated point image on the near point side, wavefront aberration measurement is performed using light in the visible region (for example, light from the light source 61A).

[0151] 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.

[0152] 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.

[0153] The Zernike polynomial fitting processing unit 133E calculates the refractive power of the subject's eye E for each point image group specified by the point image group specifying unit 133D, similarly to the Zernike polynomial fitting processing unit 131C.

[0154] exist Fig.13 Schematically shows point images acquired by the area sensor 56 in correspondence with the lens areas of the multifocal diffractive IOL of the embodiment. Fig.13 This is a diagram for the case where the number of focal points is "2".

[0155] Depending on the focal length of the IOL, the point images that make up the Hartmann image are separated into two or more separate point images. 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 that should have been formed. Depending on the structure of the optical system, the point image PI1 may be separated by making the separated point image close to the center of the Hartmann image the far point image Pf1 and making the separated point image far from the center of the Hartmann image the near point image Pn1.

[0156] The third refractive power calculation unit 133 classifies the determined two or more separation points 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 above, the point image group determination unit 133D classifies 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 for each point image group based on the wavefront aberration information obtained from the classified point image groups. The third diopter calculation unit 133 may calculate the diopter for each point image group as described above for each Hartmann image.

[0157] (Fourth Refractive Power Calculation Unit 134)

[0158] 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 for each point image group based on the wavefront aberration information obtained based on the classified point image groups. Specifically, the fourth refractive power calculation unit 134 classifies two foci of a fitted ellipse determined by performing ellipse fitting on a plurality of point images constituting the Hartmann image for each 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 for each focal length based on the classified two or more separated point images.

[0159] exist Fig.14 Shown in Figure 7 1 is a functional block diagram of a configuration example of the fourth refractive power calculation unit 134 shown in FIG.

[0160] 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.

[0161] The point image identifying unit 134A 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 134A, the Hartmann image is subjected to point image enhancement processing.

[0162] The ellipse fitting processing unit 134B performs a known ellipse fitting process on each of the plurality of point images specified by the point image specifying unit 134A to thereby specify a plurality of fitted ellipses, and specifies two foci of each of the plurality of specified fitted ellipses.

[0163] The point image group determination unit 134C determines the focal point closer to the center of the Hartmann image among the two focal points of the fitting ellipse determined by the ellipse fitting processing unit 134B as a near point image, and determines the focal point farther 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 respectively 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.

[0164] The Zernike polynomial fitting processing unit 134D calculates the refractive power of the eye to be examined E for each point image group determined by the point image group determination unit 134C, similarly to the Zernike polynomial fitting processing unit 131C.

[0165] exist Fig.15 Schematically shows point images acquired by the area sensor 56 in correspondence with the lens area of ​​the EDoF type IOL of the first embodiment.

[0166] 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 the direction connecting the far point and the near point (blurred images) due to the deep focal depth.

[0167] 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 for each point image group like a multifocal refractive IOL using the second diopter 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 for each point image group like a multifocal diffractive IOL using the third diopter calculation unit 133.

[0168] 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 to determine the fitting ellipse AC1, and determines the two focuses 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 focuses 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 focuses as the near point image and the far point image for a 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 for each point image group based on the wavefront aberration information obtained from the classified point image groups.

[0169] In addition, the diopter calculation unit 130 calculates the corneal refractive power, corneal astigmatism, and corneal astigmatism axis angle based on 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 above parameters based on the corneal curvature radius.

[0170] (Display unit 170, operation unit 180)

[0171] The display unit 170 is controlled by the control unit 110 (main control unit 111) as a user interface and displays information. The display unit 170 includes Figure 1 The display unit 10 is shown.

[0172] The display unit 170 can be controlled by the control unit 110 (main control unit 111) as a display control unit to display the processing results executed by the calculation processing unit 120. Examples of the processing results executed by the calculation processing unit 120 include one or more diopters calculated by the diopters calculation unit 130, wavefront aberration information such as a wavefront aberration map, and simulation results of viewing methods or visual acuity values.

[0173] 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 for the number of focal points of the IOL calculated by the second diopter calculation unit 132 or the third diopter calculation unit 133 for each focal length (region), and diopters on the far point side and 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 display unit 170 displays the difference between the refractive power on the farthest point side and the refractive power on the closest point side calculated by the refractive power calculation unit 130 and the difference between the refractive power on the farthest point side and the refractive power on the closest point side calculated by the fourth refractive power calculation unit 134.

[0174] The operation unit 180 is used as a user interface unit to operate the ophthalmic device. The operation unit 180 includes various hardware keys (operating levers, buttons, switches, etc.) provided on the ophthalmic device. In addition, the operation unit 180 may include various software keys (buttons, icons, menus, etc.) displayed on the touch panel display screen 10a.

[0175] 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.

[0176] (Communication Department 190)

[0177] 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 the communication method of the external device.

[0178] 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.

[0179] [Working example]

[0180] An operation example of the ophthalmologic apparatus according to the embodiment will be described.

[0181] exist Figure 16 to Figure 282 is a flowchart showing an operation example of the ophthalmologic apparatus 100 according to the embodiment.

[0182] Fig.16 The flowchart shows an operation example of the ophthalmologic apparatus 100 for calculating the refractive power of the subject's eye E using a measurement processing method corresponding to the type of IOL worn by the subject's eye E.

[0183] Figure 17-18 A flowchart showing an example of a process for measuring a single-focus IOL is shown. Specifically, Fig.17 Show Fig.16 This is a flowchart of an operation example of the monofocal IOL measurement process in step S5. Fig.18 Show Fig.17 This is a flowchart of an operation example of the single focus type calculation processing in step S15.

[0184] Figure 19 to Figure 25 A flowchart showing an operation example of multifocal IOL measurement processing. Fig.19 Show Fig.16 This is a flowchart of an operation example of the multifocal IOL measurement process in step S7.

[0185] Specifically, Figure 20 to Figure 22 An operation example of multifocal refractive IOL measurement processing is shown. Fig. 20 Show Fig.19 This is a flowchart of an operation example of the multifocal refractive IOL measurement process of step S32. Fig.21 Show Fig. 20 This is a flowchart of an operation example of the first multifocal refractive type calculation process of step S46. Fig. 22 Show Fig. 20 This is a flowchart of an operation example of the second multifocal refractive type calculation process of step S47.

[0186] in addition, Figure 23 to Figure 25 An example of a multifocal diffractive IOL measurement process is shown. Specifically, Fig.23 Show Fig.19 This is a flowchart of an operation example of the multifocal diffractive IOL measurement process of step S33. Fig.24 Show Fig.23 This is a flowchart of an operation example of the first multifocal diffraction type calculation processing of step S77. Fig.25 Show Fig.23 This is a flowchart of an operation example of the second multifocal diffraction type calculation processing of step S78.

[0187] Figure 26 to Figure 28 An example of the operation of the EDoF type IOL measurement process is shown. Specifically, Fig.26 Show Fig.16 This is a flowchart of an operation example of the EDoF type IOL measurement process in step S8. Fig. 27 Show Fig.26 This is a flowchart of an operation example of the first EDoF type calculation process of step S107. Fig.28 Show Fig.26 This is a flowchart of an operation example of the second EDoF type calculation process of step S108.

[0188] The storage unit 112 stores information for implementing Figure 16 to Figure 28 The main control unit 111 executes the processing according to the computer program. Figure 16 to Figure 28 Processing shown.

[0189] First, according to Fig.16 The flowchart of the operation example of the ophthalmic apparatus 100 shown in FIG.

[0190] (S1: Obtain IOL information)

[0191] First, the main control unit 111 acquires the IOL information worn by the eye E to be examined.

[0192] For example, the main control unit 111 controls the communication unit 190 to acquire IOL information indicating the type of IOL worn on 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 .

[0193] In some embodiments, the main control unit 111 acquires the IOL information according to the type of IOL designated based on the operation content of the user on the operation unit 180 .

[0194] In some embodiments, after the alignment described later is completed, the main control unit 111 controls the observation system 5 to obtain a transillumination image or anterior ocular image of the subject's eye E, and controls the calculation processing unit 120 to analyze the transillumination image or the anterior ocular image, thereby determining the type of IOL worn by the subject's eye E and obtaining it as IOL information. In this case, for example, the main control unit 111 can light up one of the plurality of anterior ocular illumination light sources 57, illuminate the fundus Ef with illumination light from a position away from the optical axis, and receive the return light thereof by the area sensor 56, thereby obtaining 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 and projects light onto the fundus Ef, and receives the return light thereof by the area sensor 56, thereby obtaining a transillumination image. In addition, the main control unit 111 lights up the anterior ocular illumination light source 27, and receives the return light by the area sensor 56, thereby obtaining an anterior ocular image of the subject's eye E. The main control unit 111 can determine the type of IOL worn by the inspected eye E and acquire the IOL information by using the method disclosed in Japanese Patent Application Laid-Open No. 2014-209994, for example.

[0195] (S2: Obtain pupil diameter information)

[0196] Next, the main control unit 111 acquires pupil diameter information indicating the pupil diameter of the eye E to be examined.

[0197] 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 .

[0198] In some embodiments, the main control unit 111 acquires pupil diameter information from the pupil diameter designated based on the operation content of the user on the operation unit 180 .

[0199] In some embodiments, after the alignment described below 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 to obtain the anterior ocular image of the subject's eye E, and controls the calculation processing unit 120 to analyze 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 to, for example, a brightness close to the daily brightness of the subject's eye E or a brightness of a desired state of the subject's eye E, or set to be dimmed so that analysis can be performed at any pupil diameter.

[0200] In some embodiments, pupil diameter information indicating a pupil diameter prescribed by a predetermined model eye is acquired as pupil diameter information indicating a pupil diameter of the eye to be examined E.

[0201] (S3: Alignment)

[0202] Next, with the examinee's face fixed on the face support (not shown), the examinee performs a predetermined operation on the operation unit 180 , whereby the ophthalmic apparatus 100 starts presenting a fixation mark to the examinee's eye E. Specifically, the main control unit 111 presents a fixation mark to the examinee's eye E by controlling the mark projection system 4 .

[0203] Next, with the subject's face fixed to the face support (not shown), the examiner performs a predetermined operation on the operation unit 180, whereby the ophthalmic apparatus 100 performs alignment. Thus, the head moves to the inspection position of the subject's eye E through the XY alignment performed by the XY alignment system 2 and the Z alignment performed by the Z alignment system 1. The inspection position is a position where the subject's eye E can be inspected within a predetermined accuracy.

[0204] Specifically, the main control unit 111 acquires the imaging signal of the anterior ocular image formed on the light receiving surface of the area sensor 56, and displays the anterior ocular image E' on the display unit 170 (display screen 10a of the display unit 10). Then, through the above-mentioned XY alignment and Z alignment, the head is moved to the inspection position of the inspected eye E. The movement of the head is performed by the main control unit 111 according to the instruction of the main control unit 111, but can also be performed by the main control unit 111 according to the operation or instruction of the user.

[0205] 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 origin position (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 origin position (e.g., the position equivalent to 0D) along the optical axis before performing the alignment.

[0206] (S4: Is it a monofocal IOL?)

[0207] Next, the main control unit 111 performs a measurement process corresponding to the type of IOL worn by the subject's eye E. The main control unit 111 determines the type of IOL worn by the subject's eye E based on the IOL information acquired in step S1. Here, the main control unit 111 determines whether the IOL worn by the subject's eye E is a monofocal IOL, a multifocal IOL, or an EDoF IOL. In some embodiments, when it is determined that the IOL worn by the subject's eye E is not any of the monofocal IOL, the multifocal IOL, and the EDoF IOL, the main control unit 111 causes the display unit 170 to display information corresponding to a measurement error, and stops the measurement process of the refractive power of the subject's eye E.

[0208] In step S4 , the main control unit 111 determines whether the IOL worn by the subject's eye E is a monofocal IOL based on the IOL information acquired in step S1 .

[0209] When it is determined in step S4 that the IOL worn by the subject's eye E is a monofocal IOL (S4: Yes), the operation of the ophthalmologic apparatus 100 proceeds to step S5. On the other hand, when it is determined that the IOL worn by the subject's eye E is not a monofocal IOL (S4: No), the operation of the ophthalmologic apparatus 100 proceeds to step S6.

[0210] (S5: Monofocal IOL measurement process)

[0211] If it is determined in step S4 that the IOL worn by the subject's eye E is a monofocal IOL (S4: Yes), the main control unit 111 executes monofocal IOL measurement processing. The details of step S5 will be described later. Following step S5, the operation of the ophthalmologic apparatus 100 proceeds to step S9.

[0212] (S6: Is it a multifocal IOL?)

[0213] When it is determined in step S4 that the IOL worn by the subject's eye E is not a monofocal IOL ( S4 : No), the main control unit 111 determines whether the IOL worn by the subject's eye E is a multifocal IOL based on the IOL information acquired in step S1 .

[0214] If it is determined in step S6 that the IOL worn by the subject's eye E is a multifocal IOL (S6: Yes), the operation of the ophthalmologic apparatus 100 proceeds to step S7. On the other hand, if it is determined that the IOL worn by the subject's eye E is not a multifocal IOL (S6: No), the operation of the ophthalmologic apparatus 100 proceeds to step S8.

[0215] (S7: Multifocal IOL measurement process)

[0216] If it is determined in step S6 that the IOL worn by the subject's eye E is a multifocal IOL (S6: Yes), the main control unit 111 executes a multifocal IOL measurement process. The details of step S7 will be described later. Following step S7, the operation of the ophthalmologic apparatus 100 proceeds to step S9.

[0217] (S8: EDoF type IOL measurement process)

[0218] If it is determined in step S6 that the IOL worn by the subject's eye E is not a multifocal IOL (S6: No), the main control unit 111 executes EDoF IOL measurement processing. The details of step S8 will be described later. Following step S8, the operation of the ophthalmologic apparatus 100 proceeds to step S9.

[0219] (S9: Output)

[0220] Following step S5, step S7, or step S8, the main control unit 111 causes the display unit 170 to display the diopter calculated in step S5, step S7, or step S8. In some embodiments, the main control unit 111 causes the display unit 170 to display wavefront aberration information such as a wavefront aberration map based on the measurement result obtained by the wavefront aberration measurement in association with the calculated diopter.

[0221] With the above, the operation of the ophthalmologic apparatus 100 is completed (End).

[0222] [Monofocal IOL measurement and processing]

[0223] exist Fig.16 In step S5, according to Fig.17The process shown executes the monofocal IOL measurement process. In the case where the IOL worn by the subject's eye E is a monofocal IOL, the IOL has a single focal length, so a single diopter is calculated based on the point image constituting the Hartmann image. In the monofocal IOL measurement process, after the focus lens is moved based on the diopter obtained by performing a preliminary measurement on the subject's eye E, a formal measurement is performed on the subject's eye E to calculate the diopter. That is, the focus lens is moved to a position corresponding to the focal length of the IOL worn by the subject's eye E, and a single diopter is calculated based on the acquired Hartmann image.

[0224] (S11: Obtaining Hartmann Image)

[0225] exist Fig.16 In step S5, first, the main control unit 111 performs a preliminary measurement.

[0226] Specifically, the main control unit 111 turns on the light source 61B to irradiate the inspected eye E with near-infrared light while presenting an optotype to the inspected eye E in the optotype chart 42 , and the area sensor 76 detects a Hartmann image (point image group) based on the return light from the inspected eye E.

[0227] (S12: Calculate diopter)

[0228] 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 collimating 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.

[0229] (S13: Move the focus lens)

[0230] 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 based on the movement amount corresponding to the diopter (spherical power S) calculated in step S12. In conjunction with this, the moving unit 46 and the moving unit 69 also move in the optical axis direction by the movement amount corresponding to the above-mentioned diopter.

[0231] In some embodiments, after the above movement, the main control unit 111 further determines whether the movement of the moving unit 77 or the like determined by the preliminary measurement is the first time. When it is determined that the movement is the first time, Fig.16 The processing of step S5 is transferred to step S11, where a preliminary measurement is performed. When it is determined that the movement is not the first time, Fig.16 The processing of step S5 is transferred to step S14.

[0232] (S14: Obtaining Hartmann Image)

[0233] Next, the main control unit 111 moves the moving unit 46 further in the optical axis direction from the position corresponding to the far point moved in step S13 by a distance corresponding to the predetermined diopter, so that the eye E under examination can see the sight mark in a foggy manner. In addition, if it is determined that the eye under examination wearing the IOL has no accommodation power, the fogging function can be omitted.

[0234] As a main measurement, the main control unit 111 turns on the light source 61B to irradiate the inspected eye E with near-infrared light, and detects a Hartmann image (point image group) based on the return light from the inspected eye E with the area sensor 76 .

[0235] (S15: Single-focus calculation processing)

[0236] 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. The diopter calculation unit 130 performs a single focus calculation process to calculate the diopter of the eye to be examined E. The diopter calculated in step S15 includes the spherical power (S), the cylindrical power (astigmatism power) (C), and the astigmatism axis angle (A). The details of step S15 will be described later.

[0237] above, Fig.16 Step S5 ends (End).

[0238] exist Fig.17 In step S15, according to Fig.18 The illustrated flow performs single-focus type computing processing.

[0239] (S21: Determine point image)

[0240] exist Fig.17 In step S15 , first, the main control unit 111 controls the point image determining unit 131A of the first refractive power calculation unit 131 to determine the point images constituting the Hartmann image acquired in step S14 .

[0241] (S22: Determine representative position)

[0242] 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 S21 .

[0243] (S23: Zernike polynomial fitting process)

[0244] 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 S22 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.

[0245] (S24: Calculation of diopter (SCA))

[0246] Next, the main control unit 111 controls the first refractive power 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 through the Zernike polynomial fitting process performed in step S23.

[0247] above, Fig.17 The single focus type calculation processing of step S15 is completed (End).

[0248] [Multifocal IOL measurement and processing]

[0249] exist Fig.16 In step S7, according to Fig.19 The flow shown executes a multifocal IOL measurement process. In the multifocal IOL measurement process, a multifocal refractive IOL measurement process or a multifocal diffractive IOL measurement process is executed.

[0250] [Multifocal refractive IOL measurement and processing]

[0251] In the case where the IOL worn by the subject's eye E is a multifocal refractive IOL, the IOL has focal lengths, so multiple diopters corresponding to the multiple focal lengths are calculated. In the multifocal refractive IOL measurement process, the focus lens is moved to a position corresponding to the average degree of the multiple focal lengths obtained by performing a preliminary measurement on the subject's eye E, and then a formal measurement is performed on the subject's eye E, and the diopters are calculated for each focal length. Alternatively, after the focus lens is moved to positions corresponding to the multiple focal lengths, the diopters are calculated at each position. That is, the focus lens is moved to a position corresponding to the average focal length of the IOL worn by the subject's eye E or a position corresponding to the focal length of the IOL, and the diopters are calculated for each focal length of the IOL.

[0252] (S31: Is it a multifocal refractive IOL?)

[0253] In step S7 , the main control unit 111 determines whether the IOL worn by the subject's eye E is a multifocal refractive IOL based on the IOL information acquired in step S1 .

[0254] In step S31, when it is determined that the type of IOL worn by the subject's eye E is a multifocal refractive IOL (S31: Yes), Fig.16 The processing of step S7 is transferred to step S32. On the other hand, when it is determined that the type of IOL worn by the subject's eye E is not a multifocal refractive IOL (S31: No), Fig.16 The processing of step S7 is transferred to step S33.

[0255] (S32: Multifocal Refractive IOL Measurement Process)

[0256] When it is determined in step S32 that the type of IOL worn by the subject's eye E is a multifocal refractive IOL (S32: YES), the main control unit 111 executes a multifocal refractive IOL measurement process. The details of step S32 will be described later.

[0257] Then in step S32, Fig.16 The processing of step S7 is completed (End).

[0258] (S33: Multifocal Diffractive IOL Measurement Process)

[0259] When it is determined in step S32 that the type of IOL worn by the subject's eye E is not a multifocal refractive IOL (S32: No), the main control unit 111 executes a multifocal diffractive IOL measurement process. The details of step S33 will be described later.

[0260] Then in step S33, Fig.16 The processing of step S7 is completed (End).

[0261] exist Fig.19 In step S32, according to Fig. 20 The illustrated flow executes a multifocal refractive IOL measurement process.

[0262] (S41: Acquiring Hartmann Image)

[0263] exist Fig.19 In step S32 , first, the main control unit 111 performs preliminary measurement similarly to step S11 .

[0264] Specifically, the main control unit 111 turns on the light source 61B to irradiate the eye E with near-infrared light while the eye chart 42 presents the eye to be examined. The area sensor 76 detects a Hartmann image (point image group) based on the return light from the eye E to be examined.

[0265] (S42: Calculation of diopter)

[0266] Next, similar to step S12, the main control unit 111 causes the refractive power calculation unit 130 to calculate the refractive power based on the intervals between 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 collimating lens 74 serving as the focusing lens (equivalent to the movement amount of the focusing lens) based on the calculated refractive power.

[0267] (S43: Move focus lens)

[0268] Similar to step S13, 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 based on the movement amount corresponding to the diopter (spherical power S) calculated in step S42. In conjunction with this, the moving unit 46 and the moving unit 69 each move in the optical axis direction by the movement amount corresponding to the above-mentioned diopter.

[0269] (S44: Obtaining Hartmann Image)

[0270] Next, similarly to step S14, the main control unit 111 causes the moving unit 46 to further move in the optical axis direction from the position corresponding to the far point moved in step S33 by a distance corresponding to the predetermined focal length, so that the eye under examination E can see the sight mark in a foggy manner. In addition, if it is determined that the eye under examination wearing the IOL has no accommodative power, the fogging function can be omitted.

[0271] As a main measurement, the main control unit 111 turns on the light source 61B to irradiate the inspected eye E with near-infrared light, and detects a Hartmann image (point image group) based on the return light from the inspected eye E with the area sensor 76 .

[0272] (S45: Is the formal measurement one time?)

[0273] Since a multifocal IOL has multiple focal points, if the diopter is obtained by only one formal measurement, the measurement accuracy may be reduced. Therefore, the main control unit 111 performs multiple formal measurements when predetermined conditions are met. Examples of the predetermined conditions include a first condition related to the diopter difference, a second condition related to the number of identifiable point images in the Hartmann image, and the like.

[0274] An example of the first condition is "it is determined that the difference in the refractive power of the multiple focal lengths of the IOL is large". When it is determined that the difference in the refractive power of the multiple focal lengths of the IOL is large (that is, when the first condition is satisfied), the main control unit 111 performs a plurality of formal measurements. When it is determined that the difference in the refractive power of the multiple focal lengths of the IOL is not large (that is, when the first condition is not satisfied), the main control unit 111 performs only one formal measurement.

[0275] For example, the main control unit 111 controls the diopter calculation unit 130 to calculate the diopter of each of the plurality of focal lengths in the preliminary measurement, and calculate the average diopter of the calculated plurality of diopters. The main control unit 111 moves the moving unit 77 (the collimating lens 74 as a focusing lens) along the optical axis to a position corresponding to the calculated average diopter. Then, the main control unit 111 acquires the Hartmann image of the eye E to be examined, calculates the diopter of each of the plurality of focal points based on the acquired Hartmann image, and calculates the diopter difference between the maximum diopter and the minimum diopter among the calculated plurality of diopters. When the calculated diopter difference is greater than a predetermined threshold, the main control unit 111 performs a plurality of formal measurements at positions corresponding to the focal lengths, respectively, and calculates the diopter of each of the plurality of focal points. In addition, when the calculated diopter difference is less than a predetermined threshold, the main control unit 111 performs only one formal measurement and calculates a single diopter.

[0276] When the focal number of the IOL worn by the examined eye E is "2", for example, the main control unit 111 performs multiple formal measurements when the diopter difference is 4D (Diopter; focal power) or more, and performs only one formal measurement when the diopter difference is less than 4D.

[0277] An example of the second condition is "it is determined that the number of point images that can be determined from the Hartmann image is small". When it is determined that the number of point images that can be determined from the acquired Hartmann image is small (that is, when the second condition is not satisfied), the main control unit 111 performs a plurality of formal measurements. When it is determined that the number of point images that can be determined from the acquired Hartmann image is not small (that is, when the second condition is not satisfied), the main control unit 111 performs only one formal measurement.

[0278] For example, the main control unit 111 controls the diopter calculation unit 130 to calculate the diopter of each of the multiple focal lengths in the preliminary measurement, and calculate the average diopter of the calculated multiple diopters. The main control unit 111 moves the moving unit 77 (the collimating lens 74 as a focusing lens) along the optical axis to a position corresponding to the calculated average diopter. Thereafter, the main control unit 111 acquires the Hartmann image of the eye E to be examined, and determines the point images in the acquired Hartmann image. When the number of determined point images is below a predetermined threshold, the main control unit 111 performs multiple formal measurements at positions corresponding to the focal lengths, and calculates the diopter of each of the multiple focal lengths. In addition, when the number of determined point images exceeds a predetermined threshold, the main control unit 111 performs only one formal measurement, and calculates a single diopter.

[0279] When the focal number of the IOL worn by the examined eye E is "2", for example, the main control unit 111 performs multiple formal measurements when the number of identifiable point images relative to the number of point images within the pupil diameter is less than 50%, and only performs one formal measurement when the number of identifiable point images relative to the number of point images within the pupil diameter exceeds 50%.

[0280] In step S45, the main control unit 111 determines whether the main measurement is performed only once based on the first condition or the second condition. If it is determined in step S45 that the main measurement is performed only once (S45: Yes), Fig.19 The processing of step S32 is transferred to step S46. On the other hand, when it is determined in step S45 that multiple formal measurements are performed (S45: No), Fig.19 The processing of step S32 is transferred to step S47.

[0281] (S46: First multifocal refractive type calculation process)

[0282] When it is determined in step S45 that only one formal measurement is performed (S45: Yes), the main control unit 111 performs the first multifocal refractive type calculation processing based on the intervals of the point images constituting the Hartmann image acquired in step S44, and calculates the refractive power of the eye E to be examined. The refractive power calculated in step S46 includes the spherical power (S), the cylindrical power (astigmatism power) (C), and the astigmatism axis angle (A). The details of step S46 are described later. In step S46, the focus lens is moved to a position corresponding to the refractive power (the average power of multiple focal lengths of the IOL) calculated based on the Hartmann image acquired through the preliminary measurement (for example, the Hartmann image acquired in step S44), and the refractive power is calculated based on the Hartmann image acquired at this position. Following step S46, Fig.19 Step S32 ends (End).

[0283] (S47: Second multifocal refractive type calculation process)

[0284] When it is determined in step S45 that multiple formal measurements have been performed (S45: No), the main control unit 111 performs the second multifocal refractive type calculation process to calculate the diopter of the eye under examination E. The diopter calculated in step S47 includes the spherical power (S), the cylindrical power (astigmatism power) (C), and the astigmatism axis angle (A). The details of step S47 will be described later. Following step S47, Fig.19 The processing of step S32 is completed (End).

[0285] exist Fig. 20 In step S46, according to Fig.21 The illustrated flow executes a first multifocal refractive type calculation process.

[0286] (S51: Determine point image)

[0287] exist Fig. 20 In step S46, first, the main control unit 111 controls the point image determination unit 132A of the second refractive power calculation unit 132 to determine the point images constituting the Hartmann image acquired in step S44. In some embodiments, the main control unit 111 controls the second refractive power calculation unit 132 to perform point image enhancement processing on the Hartmann image acquired in step S44, and then controls the point image determination unit 132A as described above.

[0288] (S52: Determine representative position)

[0289] 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 S51 .

[0290] (S53: Determine point image group)

[0291] Next, the main control unit 111 controls the point image group determination unit 132C to determine, based on the representative position determined in step S52, in which area of ​​the multiple areas predetermined for each focal length of the IOL the point images constituting the Hartmann image are located. Here, if the position of the IOL in the pupil can be determined, then the positional relationship indicating where the multiple areas (focal areas) for each focal length of the IOL are respectively configured is known. Therefore, the point image group determination unit 132C can determine in which area the representative position of the point image is configured, based on the IOL type determined based on the IOL information. The point image group determination unit 132C classifies the point images according to each focal length (each area) of the IOL (refer to Fig.10 and Fig.11 ). The point image group determination unit 132C may determine the point image group by determining 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.

[0292] For example, when the number of focal points of the IOL worn by the eye under examination E 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 under examination E 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 under examination E is 4 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.

[0293] (S54: Execute Zernike polynomial fitting process for each point image group)

[0294] Next, the main control unit 111 controls the Zernike polynomial fitting processing unit 132D to perform Zernike polynomial fitting processing for each point image group determined in step S53, thereby calculating wavefront aberration information (wavefront fitting formula) represented by Zernike coefficients and Zernike polynomials for each point image group. The Zernike polynomial fitting processing unit 132D uses the pupil diameter information acquired in step S2 to normalize each information of the wavefront aberration information calculated for each point image group.

[0295] (S55: Calculate the diopter (SCA) for each point image group)

[0296] 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 for each point image group through well-known calculations based on the Zernike coefficients obtained by the Zernike polynomial fitting process performed on each point image group in step S54.

[0297] above, Fig. 20 The first multifocal refractive type calculation process of step S46 is completed (End).

[0298] exist Fig. 20 In step S47, according to Fig. 22 The illustrated flow executes the second multifocal refractive type calculation process.

[0299] (S61: Move focus lens)

[0300] exist Fig. 22In step S61, the main control unit 111 moves the moving unit 77 (collimator lens 74 as a focus lens) along the optical axis to positions corresponding to the plurality of focal lengths of the IOL, and sequentially acquires Hartmann images at each position.

[0301] First, 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 one of the multiple focal lengths of the IOL. In conjunction with this, the moving units 46 and 69 also move in the optical axis direction by the amount of movement corresponding to the above-mentioned diopter.

[0302] (S62: Obtaining Hartmann Image)

[0303] Next, similarly to step S14, the main control unit 111 moves the moving unit 46 further in the optical axis direction from the position moved in step S63 by a distance corresponding to the predetermined focal power, so that the eye E under examination can see the sight mark in a foggy manner. In addition, if it is determined that the eye under examination wearing the IOL has no accommodative power, the fogging function can be omitted.

[0304] As a main measurement, the main control unit 111 turns on the light source 61B to irradiate the inspected eye E with near-infrared light, and detects a Hartmann image (point image group) based on the return light from the inspected eye E with the area sensor 76 .

[0305] (S63: Is there a next one?)

[0306] The main control unit 111 acquires Hartmann images at all positions of the multiple focal lengths of the IOL. If step S62 is not executed for all the multiple focal lengths of the IOL, the main control unit 111 determines to move the focus lens to the next focal position. If step S62 is executed for all the multiple focal lengths of the IOL, the main control unit 111 determines to move the focus lens to the next focal position.

[0307] When it is determined in step S63 that the focus lens is to be moved to the next focus position (S63: Yes), Fig. 20 The processing of step S47 is transferred to step S61. On the other hand, when it is determined that the focus lens is not to be moved to the next focus position (S63: No), Fig. 20 The processing of step S47 is transferred to step S64.

[0308] (S64: Executing the first multifocal refractive type calculation process for each focal length)

[0309] When it is determined in step S63 that the focus lens is not moved to the next focus position (S63: No), the main control unit 111 performs the first multifocal refractive type calculation process for each focal length of the IOL based on the Hartmann image repeatedly acquired in step S62. Fig.21 The first multifocal refractive calculation process shown calculates the diopter of the examinee's eye E for each focal length. The calculated diopter may be the diopter at the position corresponding to each focal length, or the diopter of all groups may be calculated.

[0310] above, Fig. 20 The second multifocal refractive type calculation process of step S47 is completed (End).

[0311] [Multifocal Diffractive IOL Measurement Process]

[0312] In the case where the IOL worn by the subject's eye E is a multifocal diffractive IOL, for example, the point images constituting the Hartmann image are separated, the separated point images are classified according to each focal length of the IOL, and multiple diopters are calculated for each focal length based on the classified two or more separated point images. That is, the focus lens is moved to a position corresponding to the average focal length of the IOL worn by the subject's eye E or a position corresponding to the focal length of the IOL, and the diopters are calculated based on the two or more separated point images separated from the point images constituting the acquired Hartmann image. In the multifocal diffractive IOL measurement process, for example, by switching the light source and changing the measurement wavelength, multiple diopters of the subject's eye E are calculated.

[0313] exist Fig.19 In step S33, according to Fig.23 The illustrated flow executes a multifocal diffractive IOL measurement process.

[0314] (S71: Switching light source)

[0315] exist Fig.19 In step S33 , first, 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.

[0316] In some embodiments, in order to reduce the load of the analysis process and shorten the analysis time, the light source switching in step S71 is performed after the preliminary measurement in step S75 or step 72. In this case, in the first measurement using near-infrared light, only point images at a distance are obtained, or even if point images at a nearby location are obtained, the intensity of the point images is weak, so it is easy to select only point images at a distance, and the determination and analysis of point images become easy, which can reduce the processing time, and can reduce the load of visible light on the human eye, and can avoid pupil constriction before the formal measurement.

[0317] (S72: Obtaining Hartmann Image)

[0318] Next, similarly to step S11 , the main control unit 111 performs preliminary measurement.

[0319] Specifically, the main control unit 111 turns on the light source 61A to irradiate the inspected eye E with visible light, and the area sensor 76 detects a Hartmann image (point image group) based on the return light from the inspected eye E. Thus, wavefront aberration measurement is performed using visible light.

[0320] (S73: Calculation of diopter)

[0321] Next, similarly to step S12, 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 to determine the movement amount of the moving unit 77 including the collimating lens 74 as the focus lens (equivalent to the movement amount of the focus lens) based on the calculated diopter. In the case where the point images are not separated, the diopter is calculated based on the obtained point images and the movement amount is determined. In the case where the point images are separated, the diopter is calculated using a group corresponding to distant points (for example, points close to the center of the area depicted by the Hartmann image) and a group corresponding to nearby points (for example, points far from the center of the area depicted by the Hartmann image), and the movement amount is determined based on the average value thereof. Alternatively, the diopter may be calculated using only the group corresponding to distant points or only the group corresponding to nearby points, and the movement amount may be determined based on the average value thereof.

[0322] (S74: Move focus lens)

[0323] Similar to step S13, 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 based on the movement amount corresponding to the diopter (spherical power S) calculated in step S73. In conjunction with this, the moving unit 46 and the moving unit 69 also move in the optical axis direction by the movement amount corresponding to the above-mentioned diopter.

[0324] (S75: Obtaining Hartmann Image)

[0325] Next, similarly to step S14, the main control unit 111 moves the moving unit 46 further in the optical axis direction by a distance corresponding to the predetermined focal length from the position corresponding to the far point moved in step S74, so that the eye E under examination can see the sight mark in a foggy manner. In addition, if it is determined that the eye under examination wearing the IOL has no accommodative power, the fogging function can be omitted.

[0326] As a main measurement, the main control unit 111 turns on the light source 61A to irradiate the inspected eye E with near-infrared light, and detects a Hartmann image (point image group) based on return light from the inspected eye E with the area sensor 76 .

[0327] (S76: Is the formal measurement once?)

[0328] Next, similarly to step S45, the main control unit 111 determines whether the main measurement is performed only once based on the first condition or the second condition. If it is determined in step S76 that the main measurement is performed only once (S76: Yes), Fig.19 The processing of step S33 is transferred to step S77. On the other hand, when it is determined in step S76 that a plurality of main measurements are performed (S76: No), Fig.19 The processing of step S33 is transferred to step S78.

[0329] (S77: First Multifocal Diffraction Type Calculation Process)

[0330] When it is determined in step S76 that only one formal measurement is performed (S76: Yes), the main control unit 111 performs the first multifocal diffraction type calculation processing based on the intervals of the point images constituting the Hartmann image acquired in step S75, and calculates the refractive power of the eye E under examination. The refractive power calculated in step S46 includes the spherical power (S), the cylindrical power (astigmatism power) (C), and the astigmatism axis angle (A). The details of step S77 are described later. In step S77, the focus lens is moved to a position corresponding to the refractive power (the average power of multiple focal lengths of the IOL) calculated based on the Hartmann image acquired through the preliminary measurement (for example, the Hartmann image acquired in step S72 or step S75), and the refractive power is calculated based on the Hartmann image acquired at this position. Following step S77, Fig.19 The processing of step S33 is completed (End).

[0331] (S78: Second multi-focus diffraction type calculation process)

[0332] When it is determined in step S76 that multiple formal measurements have been performed (S76: No), the main control unit 111 performs the second multifocal diffraction type calculation processing to calculate the diopter of the eye under examination E. The diopter calculated in step S78 includes the spherical power (S), the cylindrical power (astigmatism power) (C), and the astigmatism axis angle (A). The details of step S78 will be described later. Following step S78, Fig.19 The processing of step S33 is completed (End).

[0333] exist Fig.23 In step S77, according to Fig.24 The illustrated flow executes the first multifocal diffraction type calculation processing.

[0334] (S81: Enhancement Process)

[0335] exist Fig.23In step S77, first, the main control unit 111 controls the enhancement processing unit 133A of the third diopter calculation unit 133 to perform point image (separated point image) enhancement processing on the Hartmann image acquired in step S75. Thus, it is easy to identify two or more separated point images (especially separated point images on the near point side) formed by separation of the point images constituting the Hartmann image.

[0336] (S82: Determine point image)

[0337] 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 separate point image enhancement process has been performed in step S81 .

[0338] (S83: Determine representative position)

[0339] 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 S82 .

[0340] (S84: Determine point image group)

[0341] Next, the main control unit 111 controls the point image group determination unit 133D to separate the point images into point image groups for each focal length of the IOL based on the representative position determined in step S83. The point image group determination unit 132C classifies the separated point images determined in step S82 into any one of two or more point image groups determined according to the IOL type determined by the IOL information.

[0342] For example, when the number of focal points of the IOL worn by the eye E to be examined is "2", the point image group determination unit 133D classifies the multiple separated point images determined in step S82 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 examined is "3", the point image group determination unit 133D classifies the multiple separated point images determined in step S82 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 examinee eye E is 4 or more, the point image group determination unit 133D classifies the multiple separated point images determined in step S82 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, to determine 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.

[0343] (S85: Execute Zernike polynomial fitting process for each point image group)

[0344] Next, the main control unit 111 controls the Zernike polynomial fitting processing unit 133E to perform Zernike polynomial fitting processing for each point image group determined in step S84, thereby calculating wavefront aberration information (wavefront fitting formula) represented by Zernike coefficients and Zernike polynomials for each 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 for each point image group.

[0345] (S86: Calculate the diopter (SCA) for each point image group)

[0346] Next, the main control unit 111 controls the third refractive power calculation unit 133 to calculate the spherical power S, astigmatism power C and astigmatism axis angle A for each point image group through well-known calculations based on the Zernike coefficients obtained by the Zernike polynomial fitting process performed on each point image group in step S85.

[0347] above, Fig.23 The first multifocal diffraction type calculation process of step S77 is completed (End).

[0348] exist Fig.23 In step S78, according to Fig.25 The illustrated flow executes the second multifocal diffraction type calculation processing.

[0349] (S91: Move focus lens)

[0350] exist Fig.23 In step S78, the main control unit 111 moves the moving unit 77 (collimator lens 74 as a focus lens) along the optical axis to positions corresponding to the plurality of focal lengths of the IOL, and sequentially acquires Hartmann images at each position.

[0351] First, 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 one of the multiple focal lengths of the IOL. In conjunction with this, the moving units 46 and 69 also move in the optical axis direction by the amount of movement corresponding to the above-mentioned diopter.

[0352] (S92: Obtaining Hartmann Image)

[0353] Next, similarly to step S14, the main control unit 111 moves the moving unit 46 further in the optical axis direction from the position moved in step S91 by a distance corresponding to the predetermined focal length, so that the eye E can see the sight mark in a foggy manner. In addition, if it is determined that the eye wearing the IOL has no accommodative power, the fogging function can be omitted.

[0354] As a main measurement, the main control unit 111 turns on the light source 61A to irradiate the inspected eye E with near-infrared light, and detects a Hartmann image (point image group) based on return light from the inspected eye E with the area sensor 76 .

[0355] (S93: Is there a next one?)

[0356] The main control unit 111 acquires Hartmann images at all positions of the multiple focal lengths of the IOL. If step S92 is not executed for all the multiple focal lengths of the IOL, the main control unit 111 determines to move the focus lens to the next focal position. If step S92 is executed for all the multiple focal lengths of the IOL, the main control unit 111 determines not to move the focus lens to the next focal position.

[0357] When it is determined in step S93 that the focus lens is to be moved to the next focus position (S93: Yes), Fig.23 The processing of step S78 is transferred to step S91. On the other hand, when it is determined that the focus lens is not to be moved to the next focus position (S93: No), Fig.23 The processing of step S78 is transferred to step S94.

[0358] (S94: Execute the first multi-focus diffraction type calculation process for each focal length)

[0359] If it is determined in step S93 that the focus lens is not to be moved to the next focus position (S93: No), the main control unit 111 performs the first multifocal diffraction type calculation process for each focal length of the IOL based on the Hartmann image repeatedly acquired in step S92. Fig.24 The first multifocal diffraction calculation process shown calculates the diopter of the subject's eye E for each focal length. The calculated diopter may be the diopter at the position corresponding to each focal length, or the diopter of all groups may be calculated.

[0360] above, Fig.23 The second multifocal diffraction type calculation process of step S78 is completed (End).

[0361] [EDoF IOL measurement process]

[0362] exist Fig.16 In step S8, according to Fig.26The process shown executes the EDoF type IOL measurement process. In the case where the IOL worn by the subject's eye E is an EDoF type IOL, the diopter of the subject's eye E is calculated as a diffractive type IOL. In this case, for example, two foci of a fitted ellipse determined by performing ellipse fitting on a plurality of point images constituting the Hartmann image are classified for each focal length, and based on the classified two or more separate point images, multiple diopters including a diopter corresponding to a far point and a diopter corresponding to a near point are calculated for each focal length. That is, the focusing lens is moved to a position corresponding to the average focal length of the IOL worn by the subject's eye E or to a position corresponding to the focal length of the IOL, and the diopter is calculated based on the two foci of the fitted ellipse determined by performing ellipse fitting on the point images constituting the acquired Hartmann image. In the EDoF type measurement process, for example, the measurement wavelength is changed by switching the light source to calculate multiple diopters of the subject's eye E.

[0363] In some embodiments, when the IOL worn by the subject's eye E is an EDoF IOL, the diopter of the subject's eye E is calculated as a refractive IOL. In this case, the diopter of the subject's eye E is calculated in the same manner as the multifocal refractive IOL described above.

[0364] (S101: Switching light source)

[0365] exist Fig.16 In step S8, first, similarly to step S71, 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. In some embodiments, in order to reduce the load of the analysis process and shorten the analysis time, after the preliminary measurement in step S105 or step 102, the light source switching in step S71 is performed. In this case, in the first measurement using near-infrared light, only point images at a distance are obtained, or even if point images with influence at a nearby location are obtained, the intensity of the point images is weak, so point images with only influence at a distance are obtained, and the determination and analysis of the point images become easy, which can reduce the processing time, and can reduce the load of visible light on the human eye, and can avoid miosis before the formal measurement.

[0366] (S102: Obtaining Hartmann Image)

[0367] Next, similarly to step S72 , the main control unit 111 performs preliminary measurement.

[0368] Specifically, the main control unit 111 turns on the light source 61A to irradiate the inspected eye E with visible light, and detects a Hartmann image (point image group) based on the return light from the inspected eye E with the area sensor 76 .

[0369] (S103: Calculate diopter)

[0370] Then, similar to step S73, the main control unit 111 causes the refractive power calculation unit 130 to calculate the refractive power 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 collimating lens 74 serving as the focusing lens (equivalent to the movement amount of the focusing lens) according to the calculated refractive power.

[0371] (S104: Move focus lens)

[0372] Similar to step S74, 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 based on the movement amount corresponding to the diopter (spherical power S) calculated in step S103. In conjunction with this, the moving unit 46 and the moving unit 69 also move in the optical axis direction by the movement amount corresponding to the above-mentioned diopter.

[0373] (S105: Obtaining Hartmann Image)

[0374] Next, similarly to step S75, the main control unit 111 moves the moving unit 46 further in the optical axis direction by a distance corresponding to the predetermined focal power from the position corresponding to the far point moved in step S104, so that the eye E under examination can see the sight mark in a foggy manner. In addition, if it is determined that the eye under examination wearing the IOL has no accommodative power, the fogging function can be omitted.

[0375] As a main measurement, the main control unit 111 turns on the light source 61A to irradiate the inspected eye E with near-infrared light, and detects a Hartmann image (point image group) based on return light from the inspected eye E with the area sensor 76 .

[0376] (S106: Is the formal measurement once?)

[0377] Next, similarly to step S76, the main control unit 111 determines whether or not the main measurement is to be performed only once based on the first condition or the second condition. If it is determined in step S106 that the main measurement is to be performed only once (S106: Yes), Fig.16 The processing of step S8 is transferred to step S107. On the other hand, when it is determined in step S106 that multiple main measurements are performed (S106: No), Fig.16 The processing of step S8 is transferred to step S108.

[0378] (S107: First EDoF type calculation process)

[0379] When it is determined in step S106 that only one formal measurement is performed (S106: Yes), the main control unit 111 performs the first EDoF type calculation processing based on the interval of the point images constituting the Hartmann image acquired in step S105, and calculates the refractive power of the eye E to be examined. The refractive power calculated in step S107 includes the spherical power (S), the cylindrical power (astigmatism power) (C), and the astigmatism axis angle (A). The details of step S107 are described later. In step S107, the focus lens is moved to a position corresponding to the refractive power (the average power of multiple focal lengths of the IOL) calculated based on the Hartmann image obtained by the preliminary measurement (for example, the Hartmann image acquired in step S102 or step S105), and the refractive power can be calculated based on the Hartmann image acquired at this position. Following step S107, Fig.16 The processing of step S8 is completed (End).

[0380] (S108: Second EDoF type calculation process)

[0381] When it is determined in step S106 that multiple formal measurements have been performed (S106: No), the main control unit 111 performs the second EDoF type calculation process to calculate the diopter of the eye under examination E. The diopter calculated in step S108 includes the spherical power (S), the cylindrical power (astigmatism power) (C), and the astigmatism axis angle (A). The details of step S108 will be described later. Following step S108, Fig.16 The processing of step S8 is completed (End).

[0382] exist Fig.26 In step S107, according to Fig. 27 The shown flow executes a first EDoF type calculation process.

[0383] (S111: Determine point image)

[0384] exist Fig.26 In step S107, first, the main control unit 111 controls the point image determination unit 134A of the fourth diopter calculation unit 134 to determine the point images constituting the Hartmann image acquired in step S105. In some embodiments, the main control unit 111 controls the fourth diopter calculation unit 134 to perform point image enhancement processing on the Hartmann image acquired in step S105, and then controls the point image determination unit 134A as described above.

[0385] (S112: Is it configured in each area?)

[0386] Then, if Fig.10 or Fig.11As shown, the main control unit 111 determines whether the plurality of point images determined in step S111 are arranged in each region corresponding to the focal length of the IOL. 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 S111 similarly to step S52, and determines whether the point image is arranged in each region corresponding to the focal length of the IOL based on the determined representative position similarly to step S53.

[0387] When it is determined that the determined plurality of point images are arranged in each region corresponding to the focal length of the IOL (S112: Yes), Fig.26 The processing of step S107 is transferred to step S113. 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 (S112: No), Fig.26 The processing of step S107 is transferred to step S114.

[0388] (S113: First multifocal refractive type calculation process)

[0389] When it is determined in step S112 that the determined plurality of point images are arranged in each region corresponding to the focal length of the IOL (S112: Yes), the main control unit 111 controls the second refractive power calculation unit 132 to execute the first multifocal refractive type calculation process for calculating the refractive power of the subject's eye E based on the point images determined in step S111. Fig.21 The flow shown in the figure performs the first multifocal refractive type calculation process. Fig.26 The processing of step S107 is completed (End).

[0390] (S114: Do you want to separate the point image?)

[0391] When it is determined in step S112 that the plurality of point images determined are not arranged in each area corresponding to the focal length of the IOL (S112: No), the main control unit 111 determines that the plurality of point images determined in step S111 are Fig.13 It is shown whether the number of point images greater than or equal to a predetermined threshold value among the plurality of point images constituting the Hartmann image is separated into two or more separated point images.

[0392] When it is determined that the number of point images equal to or greater than the predetermined threshold value among the plurality of point images determined is separated into two or more separated point images (S114: Yes), Fig.26 The processing of step S107 is transferred to step S115. When it is determined that the number of point images above the predetermined threshold value among the determined plurality of point images is not separated into two or more separated point images (S114: No), Fig.26 The processing of step S107 is transferred to step S116.

[0393] (S115: First Multifocal Diffraction Type Calculation Process)

[0394] When it is determined in step S114 that the number of point images that are greater than or equal to the predetermined threshold value among the plurality of point images determined is separated into two or more separated point images (S114: Yes), the main control unit 111 controls the third refractive power calculation unit 133 to execute the first multifocal diffractive type calculation process for calculating the refractive power of the subject's eye E based on the point images determined in step S111. 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 S111. Fig.24 The process shown in the figure performs the first multi-focus diffraction type calculation process. Fig.26 The processing of step S107 is completed (End).

[0395] (S116: Ellipse Fitting Process)

[0396] When it is determined in step S114 that the number of point images above the predetermined threshold value among the determined multiple point images is separated into two or more separated point images (S114: 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 S111. The ellipse fitting processing unit 134B determines multiple fitting ellipses for each of the multiple point images determined in step S111, and determines two foci for each of the determined multiple fitting ellipses.

[0397] (S117: Determine point image group)

[0398] Next, the main control unit 111 controls the point image group determination unit 134C to determine the focal point close to the center of the Hartmann image among the two focal points of the fitting ellipse determined in step S116 as the near point image, and to determine the focal point 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 respectively 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.

[0399] (S118: Execute Zernike polynomial fitting process for each point image group)

[0400] Next, the main control unit 111 controls the Zernike polynomial fitting processing unit 134D to perform Zernike polynomial fitting processing for each point image group determined in step S117, thereby calculating wavefront aberration information (wavefront fitting formula) represented by Zernike coefficients and Zernike polynomials for each point image group. The Zernike polynomial fitting processing unit 134D normalizes the wavefront aberration information calculated for each point image group using the pupil diameter information acquired in step S2.

[0401] (S119: Calculate the diopter (SCA) for each point image group)

[0402] Next, the main control unit 111 controls the fourth refractive power calculation unit 134 to calculate the spherical power S, astigmatism power C and astigmatism axis angle A for each point image group through well-known calculations based on the Zernike coefficients obtained by the Zernike polynomial fitting process performed on each point image group in step S118.

[0403] above, Fig.26 The processing of step S107 is completed (End).

[0404] exist Fig.26 In step S108, according to Fig.28 The shown flow executes the second EDoF type calculation process.

[0405] (S121: Move focus lens)

[0406] exist Fig.26 In step S108 , the main control unit 111 moves the moving unit 77 (the collimator lens 74 as a focus lens) along the optical axis to positions corresponding to the plurality of focal lengths of the IOL, and sequentially acquires Hartmann images at each position.

[0407] First, 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 one of the multiple focal lengths of the IOL. In conjunction with this, the moving units 46 and 69 also move in the optical axis direction by the amount of movement corresponding to the above-mentioned diopter.

[0408] (S122: Obtaining Hartmann Image)

[0409] Next, similarly to step S92, the main control unit 111 moves the moving unit 46 further in the optical axis direction from the position moved in step S111 by a distance corresponding to the predetermined focal power, so that the eye E under examination can see the sight mark in a foggy manner. In addition, if it is determined that the eye under examination wearing the IOL has no accommodative power, the fogging function can be omitted.

[0410] As a main measurement, the main control unit 111 turns on the light source 61A to irradiate the inspected eye E with near-infrared light, and detects a Hartmann image (point image group) based on return light from the inspected eye E with the area sensor 76 .

[0411] (S123: Is there a next one?)

[0412] The main control unit 111 acquires Hartmann images at all positions of the multiple focal lengths of the IOL. If step S122 is not executed for all the multiple focal lengths of the IOL, the main control unit 111 determines to move the focus lens to the next focal position. If step S122 is executed for all the multiple focal lengths of the IOL, the main control unit 111 determines not to move the focus lens to the next focal position.

[0413] When it is determined in step S123 that the focus lens is to be moved to the next focus position (S123: Yes), Fig.26 The processing of step S108 is transferred to step S121. On the other hand, when it is determined that the focus lens is not to be moved to the next focus position (S123: No), Fig.26 The processing of step S108 is transferred to step S124.

[0414] (S124: Executing the first multi-focus diffraction type calculation process for each focal length)

[0415] If it is determined in step S123 that the focus lens is not to be moved to the next focus position (S123: No), the main control unit 111 performs the first multifocal diffraction type calculation processing for each focal length of the IOL based on the Hartmann image repeatedly acquired in step S122. Fig.24 The first multifocal diffraction calculation process shown calculates the diopter of the subject's eye E for each focal length. The calculated diopter may be the diopter at the position corresponding to each focal length, or the diopter of all groups may be calculated.

[0416] above, Fig.26 The second EDoF type calculation process of step S108 ends (End).

[0417] As described above, according to the embodiment, by changing the measurement processing method (including the diopter calculation method) according to the type of IOL worn by the examinee's eye E, the reliability of the calculation result of the diopter of the examinee's eye wearing the IOL can be improved.

[0418] (Variation Example)

[0419] The processing of the embodiment is not limited to the processing described in the above embodiment. Fig.23 Step S77 or step S78 can be performed as follows.

[0420] <First Modification>

[0421] exist Fig.29 An example of the processing flow of step S77 of the first modified example of the embodiment is shown in FIG.

[0422] The storage unit 112 stores information for implementing Fig.29 The main control unit 111 operates according to the computer program, thereby executing Fig.29 Processing shown.

[0423] (S131: Search)

[0424] As described above, when the IOL worn by the eye E to be examined is a multifocal diffractive IOL, the point image constituting the Hartmann image is separated into two or more separate point images. At this time, in most cases, the outline of the separate point image on the near side is not clear. Therefore, the main control unit 111 controls each part so that the focus lens is moved while searching for the position where the separate point image (on the near side) becomes clear.

[0425] The main control unit 111 controls the aberration measurement projection system 6 and the aberration measurement light receiving system 7 to repeatedly acquire Hartmann images while moving the moving unit 77 from the position corresponding to the far point moved in step S74 to the near point side by a predetermined step. For example, the main control unit 111 controls the diopter calculation unit 130 (the calculation processing unit 120) to perform enhancement processing on the repeatedly acquired Hartmann images. In addition, the main control unit 111 can control the light source 61A to increase the light quantity, or increase the gain of the area sensor 76, or extend the exposure time, thereby controlling the aberration measurement projection system 6 and the aberration measurement light receiving system 7 to repeatedly acquire Hartmann images.

[0426] The main control unit 111 controls the diopter calculation unit 130 (arithmetic processing unit 120) as a search processing unit, and searches for a position (position of the focus lens (moving unit 77)) at which the separated point images can be well determined by analyzing the acquired Hartmann image. In some embodiments, the diopter calculation unit 130 (arithmetic processing unit 120) determines the position at which the contrast of the separated point image with the lowest contrast among two or more separated point images separated from a point image is the highest as the position at which the separated point images can be well determined. In some embodiments, the diopter calculation unit 130 (arithmetic processing unit 120) determines the position at which the interval (interval of representative positions) between two or more separated point images is the widest as the position at which the separated point images can be well determined. In some embodiments, the diopter calculation unit 130 (arithmetic processing unit 120) determines the position at which the number of determined separated point images is the largest as the position at which the separated point images can be well determined.

[0427] (S132: Obtaining Hartmann Image)

[0428] Next, the main control unit 111 turns on the light source 61A as a main measurement to irradiate the inspected eye E with near-infrared light, and detects a Hartmann image (point image group) based on the return light from the inspected eye E with the area sensor 76 .

[0429] (S133: First Multifocal Diffraction Type Calculation Process)

[0430] The main control unit 111 performs the first multifocal diffraction type calculation processing based on the intervals of the point images constituting the Hartmann image acquired in step S132 to calculate the diopter of the eye E to be examined. The diopter calculated in step S137 includes the spherical power (S), the cylindrical power (astigmatism power) (C), and the astigmatism axis angle (A). Next, step S133 is performed. Fig.23 The processing of step S77 ends (End). In addition, when there are many points to be separated, the positions where each point becomes clear can be searched, and the diopter corresponding to each position can be calculated as the result.

[0431] <Second Modification>

[0432] Generally, it is believed that the eye to be examined wearing an IOL has no accommodation function. However, the eye to be examined wearing an IOL can have accommodation function through the movement of the ciliary muscle, etc. Therefore, in the second variant of the 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.

[0433] exist Fig.30 An example of the processing flow of step S78 of the second modification example of the embodiment is shown in FIG.

[0434] The storage unit 112 stores information for implementing Fig.30 The main control unit 111 operates according to the computer program, thereby executing Fig.30 Processing shown.

[0435] (S141: Search)

[0436] Executed before step S141 Fig.23 In step S74, the moving unit 77 (collimating lens 74 as a focus lens) is moved along the optical axis to a position corresponding to the far point based on a movement amount corresponding to the diopter (spherical power S) calculated in step S73.

[0437] In step S141 , the main control unit 111 controls each unit in the same manner as in step S131 so as to search for a position where the separated point image becomes clear while moving the focus lens.

[0438] (S142: Obtaining Hartmann Image)

[0439] The main control unit 111 moves the moving unit 46 further in the optical axis direction from the position corresponding to the far point moved in step S74 (far point position) by a distance corresponding to the predetermined focal length, so that the eye E under examination can see the sight mark in a foggy manner. In addition, if it is determined that the eye under examination wearing the IOL has no accommodative power, the fogging function can be omitted.

[0440] Next, similarly to step S132, the main control unit 111 moves the moving unit 77 to the position searched in step S141, and as a formal measurement, turns on the light source 61A to irradiate the inspected eye E with visible light, and the area sensor 76 detects the Hartmann image (point image group) based on the return light from the inspected eye E.

[0441] (S143: Move (close-up) focus lens)

[0442] The main control unit 111 moves the moving unit 77 (collimating lens 74 as a focus lens) to the near position along the optical axis. In conjunction with this, the moving unit 46 and the moving unit 69 also move in the optical axis direction by the movement amount corresponding to the above-mentioned diopter. The near position can be, for example, a fixed position such as 40 cm, a position frequently used by the subject's eye E, a near position predetermined corresponding to the IOL worn by the subject's eye E, etc.

[0443] (S144: Obtaining Hartmann Image)

[0444] Next, the main control unit 111 irradiates the inspected 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 the Hartmann image (point image group) based on the return light from the inspected eye E is detected by the area sensor 76.

[0445] (S145: First Multifocal Diffraction Type Calculation Process)

[0446] The main control unit 111 performs the first multifocal diffraction type calculation processing based on the intervals of the point images constituting the Hartmann image detected by the area sensor 76 in step S75 or step S144, and calculates the diopter of the subject's eye E. The diopter calculated in step S145 includes the spherical power (S), the cylindrical power (astigmatism power) (C), and the astigmatism axis angle (A). Following step S145, Fig.23 The processing of step S78 is completed (End).

[0447] For example, the distance diopter and the near diopter can be obtained from the Hartmann image obtained by the distance measurement, and the distance diopter and the near diopter can be obtained from the Hartmann image obtained by the near measurement. In this case, the ophthalmic device can select and output the distance diopter obtained by the distance measurement and the near diopter obtained by the near measurement.

[0448] As described above, according to a variation of the implementation method, 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 of the IOL, and the refractive power is calculated using each Hartmann image. Therefore, in a case where 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 also be improved.

[0449] In addition, as another variation of the embodiment, when the information of the near power of the IOL is known, after calculating the diopter of the far power, the focus lens can be moved by a distance equivalent to the added power of the design value, and the Hartmann image can be acquired and analyzed at this position. In addition, the focus lens can be moved sequentially by predetermined powers, for example, from +5D to -1D, etc., to acquire and analyze the Hartmann image.

[0450] [effect]

[0451] An ophthalmologic apparatus, an ophthalmologic apparatus control method, and a program according to an embodiment will be described.

[0452] A first embodiment of the present invention is an ophthalmic device (100) comprising a measuring optical system (aberration measuring projection system 6 and aberration measuring light receiving system 7), an acquisition unit (communication unit 190), a control unit (110, main control unit 111) and a calculation unit (diopter calculation unit 130). The measuring optical system comprises a focusing lens (collimating lens 74), and measures the wavefront aberration of an eye under examination (E) wearing an intraocular lens to acquire a Hartmann image. The acquisition unit acquires at least intraocular lens information representing the optical characteristics of the intraocular lens. The control unit moves the focusing lens to a position corresponding to the focal length of the intraocular lens determined based on the intraocular lens information, and acquires the Hartmann image by the measuring optical system. The calculation unit calculates the diopter of the eye under examination based on the Hartmann image using an operation processing method corresponding to the intraocular lens information.

[0453] According to this aspect, the refractive power of the subject's eye wearing the IOL is calculated using a measurement method corresponding 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.

[0454] In a second aspect of the embodiment, according to the first aspect, the acquisition unit acquires pupil diameter information indicating the pupil diameter, and the calculation unit calculates the diopter based on the Hartmann image in the area defined by the pupil diameter information.

[0455] According to such an aspect, the diopter is calculated based on the wavefront aberration information corresponding to the pupil diameter, so that the reliability of the calculation result of the diopter of the subject's eye wearing the IOL can be further improved.

[0456] In a third aspect of the embodiment, according to the first aspect or the second aspect, the intraocular lens information indicates either a monofocal type or a multifocal type.

[0457] According to this method, the refractive power of the examinee's eye wearing the IOL is calculated using a measurement method corresponding to either a monofocal IOL or a multifocal IOL, so the reliability of the calculation result of the refractive power of the examinee's eye wearing the IOL can be improved.

[0458] In a fourth aspect of the embodiment, according to the third aspect, when it is determined based on the intraocular lens information that the intraocular lens is a monofocal type intraocular lens, the control unit moves the focus lens to a position corresponding to the focal length of the intraocular lens, and the calculation unit calculates a single diopter based on the Hartmann image.

[0459] According to such an aspect, the reliability of the calculation result of the refractive power of the subject's eye wearing the monofocal IOL can be improved.

[0460] In a fifth mode of the implementation, according to the third mode or the fourth mode, when it is determined based on the intraocular lens information that the intraocular lens is a multifocal refractive type intraocular lens, the control unit moves the focus lens to a position corresponding to an average focal length of the intraocular lens or a position corresponding to a focal length of the intraocular lens, and the calculation unit calculates the refractive power for each focal length of the intraocular lens.

[0461] According to such a mode, the reliability of the calculation result of the refractive power of the subject's eye wearing the multifocal refractive IOL can be improved.

[0462] In a sixth mode of the implementation, according to any one of the third to fifth modes, when it is determined based on the intraocular lens information that the intraocular lens is a multifocal diffraction type intraocular lens, the control unit moves the focus lens to a position corresponding to an average focal length of the intraocular lens or a position corresponding to the focal length of the intraocular lens, and the calculation unit calculates the refractive power based on two or more separated point images separated from the point image constituting the Hartmann image.

[0463] According to such a mode, the reliability of the calculation result of the refractive power of the subject's eye wearing the multifocal diffractive IOL can be improved.

[0464] In a seventh aspect of the implementation mode, according to any one of the third aspect to the sixth aspect, when it is determined based on the intraocular lens information that the intraocular lens is an intraocular lens of an extended depth of field type, the control unit moves the focus lens to a position corresponding to an average focal length of the intraocular lens or a position corresponding to a focal length of the intraocular lens, and the calculation unit calculates the diopter based on two foci of a fitted ellipse determined by performing ellipse fitting on point images constituting the Hartmann image.

[0465] According to such an aspect, the reliability of the calculation result of the refractive power of the subject's eye wearing the EDoF type IOL can be improved.

[0466] An eighth embodiment of the present invention is a method for controlling an ophthalmic device (100), the ophthalmic device (100) including a measuring optical system (aberration measuring projection system 6 and aberration measuring light receiving system 7), the measuring optical system including a focusing lens (collimating lens 74), and measuring the wavefront aberration of an eye to be examined (E) wearing an intraocular lens to obtain a Hartmann image. The method for controlling the ophthalmic device includes: an acquisition step of at least obtaining intraocular lens information indicating the optical characteristics of the intraocular lens; a control step of moving the focusing lens to a position corresponding to the focal length of the intraocular lens determined based on the intraocular lens information, and obtaining a Hartmann image by the measuring optical system; and a calculation step of calculating the diopter of the eye to be examined based on the Hartmann image using a calculation processing method corresponding to the intraocular lens information.

[0467] According to such a method, the refractive power of the subject's eye wearing the IOL is calculated using a measurement method corresponding 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.

[0468] In a ninth aspect of the embodiment, according to the eighth aspect, in the acquisition step, pupil diameter information indicating the pupil diameter is acquired, and in the calculation step, the diopter is calculated based on the Hartmann image in the area defined by the pupil diameter information.

[0469] According to such a method, the diopter is calculated based on the wavefront aberration information corresponding to the pupil diameter, so the reliability of the calculation result of the diopter of the subject's eye wearing the IOL can be further improved.

[0470] In a tenth aspect of the embodiment, according to the eighth aspect or the ninth aspect, the intraocular lens information indicates either a monofocal type or a multifocal type.

[0471] According to such a method, the refractive power of the examinee's eye wearing the IOL is calculated using a measurement method corresponding to either a monofocal IOL or a multifocal IOL, so the reliability of the calculation result of the refractive power of the examinee's eye wearing the IOL can be improved.

[0472] In the eleventh mode of the implementation, according to the tenth mode, when it is determined based on the intraocular lens information that the intraocular lens is a monofocal type intraocular lens, in the control step, the focus lens is moved to a position corresponding to the focal length of the intraocular lens, and in the calculation step, a single refractive power is calculated based on the Hartmann image.

[0473] According to such a method, the reliability of the calculation result of the refractive power of the subject's eye wearing the monofocal IOL can be improved.

[0474] In the twelfth mode of the implementation, according to the tenth mode or the eleventh mode, when it is determined based on the intraocular lens information that the intraocular lens is a multifocal refractive type intraocular lens, in the control step, the focus lens is moved to a position corresponding to an average focal length of the intraocular lens or a position corresponding to a focal length of the intraocular lens, and in the calculation step, the refractive power is calculated for each focal length of the intraocular lens.

[0475] According to such a method, the reliability of the calculation result of the refractive power of the subject's eye wearing the multifocal refractive IOL can be improved.

[0476] In the thirteenth mode of the implementation, according to any one of the tenth to twelfth modes, when it is determined based on the intraocular lens information that the intraocular lens is a multifocal diffraction type intraocular lens, in the control step, the focus lens is moved to a position corresponding to the average focal length of the intraocular lens or a position corresponding to the focal length of the intraocular lens, and in the calculation step, the refractive power is calculated based on two or more separated point images separated from the point image constituting the Hartmann image.

[0477] According to such a method, the reliability of the calculation result of the refractive power of the subject's eye wearing the multifocal diffractive IOL can be improved.

[0478] In a fourteenth aspect of the embodiment, according to any one of the tenth to thirteenth aspects, when it is determined based on the intraocular lens information that the intraocular lens is an intraocular lens of an extended depth of field type, in the control step, the focus lens is moved to a position corresponding to an average focal length of the intraocular lens or a position corresponding to a focal length of the intraocular lens, and in the calculation step, the diopter is calculated based on two foci of a fitted ellipse determined by performing ellipse fitting on point images constituting the Hartmann image.

[0479] According to such a method, the reliability of the calculation result of the refractive power of the subject's eye wearing the EDoF type IOL can be improved.

[0480] A fifteenth aspect of the embodiment is a program that executes each step of the method for controlling an ophthalmologic apparatus according to any one of the eighth to fourteenth aspects.

[0481] According to such a program, the refractive power of the subject's eye wearing the IOL is calculated using a measurement method corresponding 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.

[0482] (Other Modifications)

[0483] The above-described embodiment 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.

[0484] The invention of the above-mentioned 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 photography function, anterior ocular photography 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 photography function is implemented by a fundus camera and a scanning ophthalmoscope (SLO), etc. The anterior ocular photography function is implemented by a slit lamp, etc. The OCT function is implemented by an optical coherence tomography, etc. The ultrasonic examination function is implemented by an ultrasonic diagnostic device, etc. In addition, the present invention can also be applied to a device (compound machine) having two or more of these functions.

[0485] Description of Reference Numerals

[0486] 4. Visual mark projection system

[0487] 5 Observation system

[0488] 6 Aberration measurement projection system

[0489] 7 Aberration measurement light receiving system

[0490] 61, 61A, 61B light source

[0491] 75 Hartmann Plate

[0492] 76 Area Sensor

[0493] 100 Ophthalmic Devices

[0494] 110 Control Department

[0495] 111 Main control unit

[0496] 120 Calculation processing unit

[0497] 130 Diopter calculation unit

[0498] 131 First diopter calculation unit

[0499] 131A, 132A, 133B, 134A Point image determination unit

[0500] 131B, 132B, 133C represent position determination units

[0501] 131C, 132D, 133E, 134D Zernike polynomial fitting processing unit

[0502] 132 Second diopter calculation unit

[0503] 132C, 133D, 134C Point image group determination unit

[0504] 133 Third diopter calculation unit

[0505] 133A Enhanced Processing Unit

[0506] 134 Fourth diopter calculation unit

[0507] 134B Ellipse fitting processing unit

[0508] E Eye under examination

[0509] Ef fundus.

Claims

1. An ophthalmic device comprising: measuring an optical system including a focusing lens, and measuring a wavefront aberration of a subject's eye wearing an intraocular lens to obtain a Hartmann image; an acquisition unit that acquires at least intraocular lens information indicating optical characteristics of the intraocular lens; a control unit that moves the focus lens to a position corresponding to the focal length of the intraocular lens determined based on the intraocular lens information, and causes the measurement optical system to acquire the Hartmann image; as well as The calculation unit calculates the refractive power of the eye to be examined based on the Hartmann image using an arithmetic processing method corresponding to the intraocular lens information.

2. The ophthalmic device according to claim 1, wherein: The acquisition unit acquires pupil diameter information indicating pupil diameter, The calculation unit calculates the diopter based on a Hartmann image within a region defined based on the pupil diameter information.

3. The ophthalmic device according to claim 1 or 2, characterized in that: The intraocular lens information indicates either a monofocal type or a multifocal type.

4. The ophthalmic device according to claim 3, wherein: When it is determined based on the intraocular lens information that the intraocular lens is a monofocal intraocular lens, the control unit moves the focus lens to a position corresponding to the focal length of the intraocular lens, and the calculation unit calculates a single diopter based on the Hartmann image.

5. The ophthalmic device according to claim 3, wherein: When it is determined based on the intraocular lens information that the intraocular lens is a multifocal refractive type intraocular lens, the control unit moves the focus lens to a position corresponding to an average focal length of the intraocular lens or a position corresponding to a focal length of the intraocular lens, and the calculation unit calculates the refractive power according to each focal length of the intraocular lens.

6. The ophthalmic device according to claim 3, wherein: When it is determined based on the intraocular lens information that the intraocular lens is a multifocal diffraction type intraocular lens, the control unit moves the focus lens to a position corresponding to an average focal length of the intraocular lens or a position corresponding to a focal length of the intraocular lens, and the calculation unit calculates the refractive power based on two or more separated point images separated from the point image constituting the Hartmann image.

7. The ophthalmic device according to claim 3, wherein: When it is determined based on the intraocular lens information that the intraocular lens is an intraocular lens of an extended depth of field type, the control unit moves the focus lens to a position corresponding to an average focal length of the intraocular lens or a position corresponding to a focal length of the intraocular lens, and the calculation unit calculates the diopter based on two foci of a fitted ellipse determined by performing ellipse fitting on point images constituting the Hartmann image.

8. A control method for an ophthalmic device, the ophthalmic device comprising a measuring optical system, the measuring optical system comprising a focusing lens, and measuring the wavefront aberration of an eye to be examined wearing an intraocular lens to obtain a Hartmann image, characterized in that: The control method of the ophthalmic device comprises: an acquisition step of at least acquiring intraocular lens information representing optical characteristics of the intraocular lens; a control step of moving the focus lens to a position corresponding to the focal length of the intraocular lens determined based on the intraocular lens information and causing the measuring optical system to acquire the Hartmann image; and The calculation step is to calculate the refractive power of the eye to be examined based on the Hartmann image using a calculation processing method corresponding to the intraocular lens information.

9. The control method of an ophthalmic device according to claim 8, characterized in that: In the acquisition step, pupil diameter information indicating pupil diameter is acquired, In the calculation step, the diopter is calculated based on a Hartmann image within a region defined based on the pupil diameter information.

10. The control method of an ophthalmic device according to claim 8 or 9, characterized in that: The intraocular lens information indicates either a monofocal type or a multifocal type.

11. The control method of an ophthalmic device according to claim 10, characterized in that: When it is determined based on the intraocular lens information that the intraocular lens is a monofocal type intraocular lens, in the control step, the focus lens is moved to a position corresponding to the focal length of the intraocular lens, and in the calculation step, a single diopter is calculated based on the Hartmann image.

12. The control method of an ophthalmic device according to claim 10, characterized in that: When it is determined based on the intraocular lens information that the intraocular lens is a multifocal refractive type intraocular lens, in the control step, the focus lens is moved to a position corresponding to an average focal length of the intraocular lens or a position corresponding to a focal length of the intraocular lens, and in the calculation step, the refractive power is calculated according to each focal length of the intraocular lens.

13. The control method of an ophthalmic device according to claim 10, characterized in that: When it is determined based on the intraocular lens information that the intraocular lens is a multifocal diffraction type intraocular lens, in the control step, the focus lens is moved to a position corresponding to an average focal length of the intraocular lens or a position corresponding to a focal length of the intraocular lens, and in the calculation step, the refractive power is calculated based on two or more separated point images separated from the point image constituting the Hartmann image.

14. The control method of an ophthalmic device according to claim 10, characterized in that: When it is determined based on the intraocular lens information that the intraocular lens is an intraocular lens of an extended depth of field type, in the controlling step, the focus lens is moved to a position corresponding to an average focal length of the intraocular lens or a position corresponding to a focal length of the intraocular lens, and in the calculating step, the diopter is calculated based on two foci of a fitted ellipse determined by performing ellipse fitting on point images constituting the Hartmann image.

15. A program, characterized in that The computer is caused to execute each step of the method for controlling an ophthalmologic apparatus according to claim 8 or 9.

Images