JP7201855B2 - Ophthalmic device and ophthalmic information processing program - Google Patents

Description

The present invention relates to an ophthalmologic apparatus and an ophthalmologic information processing program.

2. Description of the Related Art An ophthalmologic apparatus capable of performing multiple examinations and measurements on an eye to be examined is known. There are subjective tests and objective measurements for the tests and measurements on the subject's eye. A subjective test is one in which results are obtained based on responses from the subject. Objective measurement acquires information about the subject's eye using mainly physical techniques without referring to responses from the subject.

For example, Patent Literature 1 discloses an ophthalmologic apparatus capable of measuring the refractive power of an eye to be inspected and making measurements using optical coherence tomography. This ophthalmologic apparatus projects a ring-shaped measurement light beam onto the eye to be inspected and detects the return light to obtain the measured value of the refractive power of the eye to be inspected. The ophthalmologic apparatus can provide information for determining the reliability of the refractive power measurement value of the subject's eye by acquiring a tomographic image at the incident position of the measurement light flux on the retina.

JP 2017-136216 A

Various causes are conceivable when the results of the subjective examination do not improve despite refractive correction of the subject's eye. If the cause is in the anterior segment of the eye to be inspected, it is conceivable that the refraction of the light entering the eye is insufficient and the light is not successfully collected on the retina. If the cause is in the posterior segment of the subject's eye, it is conceivable that there is a disease in the retina and the light condensed on the retina cannot be taken in. In addition, it is conceivable that there is a cause in the nervous system or the brain.

In such cases, it is desirable for the ophthalmic device to be able to provide information to identify the cause.

However, since the conventional method is to grasp the morphology of the fundus at the incident position of the measurement light flux, it is necessary to identify whether the cause of the subjective test result not improving is in the anterior or posterior segment of the eye. It is difficult to provide information on

The present invention has been made in view of such circumstances, and an object of the present invention is to provide a new technique for identifying the cause of non-improvement of subjective test results.

A first aspect of some embodiments includes an edema identifying portion that identifies edema in the fundus based on fundus data of the subject eye collected using optical coherence tomography, an axial length in the macula, and the a measurement value correcting unit that corrects the measured value of the refractive power of the subject eye based on the distance from the retinal pigment epithelium layer to the inner limiting membrane at the edema site identified by the edema identifying unit and the macular retinal thickness; An ophthalmic device comprising:

In the ophthalmic apparatus according to the second aspect of some embodiments, in the first aspect, the axial length, which is the distance from the corneal vertex to the internal limiting membrane, is AL _ILM , the macular retinal thickness is RT, and the macula is Assuming that the height of edema is MET and the intraocular equivalent refractive index is n, the measured value correcting unit adds a correction value γ1 obtained by the following formula (A) to the measured value to obtain the measured value. correct.

In the ophthalmic apparatus according to the third aspect of some embodiments, in the first aspect, let AL _ILM be the axial length that is the distance from the corneal vertex to the internal limiting membrane, let RT be the macular retinal thickness, and When the height of edema is MET and the intraocular equivalent refractive index is n, the measured value correction unit adds a correction value γ1 obtained by the following formulas (B) and (C) to the measured value. to correct the measured value.

An ophthalmologic apparatus according to a fourth aspect of some embodiments, in any one of the first to third aspects, includes a display control unit that causes a display unit to display the measured value corrected by the measured value correction unit.

A fifth aspect of some embodiments is an edema identification step of identifying edema in the fundus based on fundus data of the eye to be examined collected using optical coherence tomography; a measured value correction step of correcting the measured value of the refractive power of the subject eye based on the distance from the retinal pigment epithelium layer to the inner limiting membrane at the edema site identified in the edema identifying step and the macular retinal thickness; is an ophthalmic information processing program that causes a computer to execute

In the ophthalmologic information processing program according to the sixth aspect of some embodiments, the axial length, which is the distance from the corneal vertex to the inner limiting membrane, is AL _ILM , the macular retinal thickness is RT, and the degree of edema in the macula is determined. MET and n is the intraocular equivalent refractive index, the measured value correction step corrects the measured value by adding a correction value γ1 obtained by the following formula (D) to the measured value. .

In the ophthalmologic information processing program according to the seventh aspect of some embodiments, the axial length of the eye, which is the distance from the corneal vertex to the inner limiting membrane, is AL _ILM , the macular retinal thickness is RT, and the degree of edema in the macula is determined. When the depth is MET and the intraocular equivalent refractive index is n, the measured value correction step is performed by adding a correction value γ1 obtained by the following formulas (E) and (F) to the measured value. Correct the measured value.

An ophthalmologic information processing program according to some embodiments, in any one of the fifth to seventh aspects, includes a display control step of causing a display unit to display the measured value corrected in the measured value correcting step.

ADVANTAGE OF THE INVENTION According to this invention, it becomes possible to provide the new technique for identifying the cause that the result of a subjective test does not improve.

1 is a schematic diagram showing a configuration example of an optical system of an ophthalmologic apparatus according to an embodiment; FIG. 1 is a schematic diagram showing a configuration example of an optical system of an ophthalmologic apparatus according to an embodiment; FIG. 1 is a schematic diagram for explaining a processing system of an ophthalmologic apparatus according to an embodiment; FIG. 1 is a schematic diagram for explaining a processing system of an ophthalmologic apparatus according to an embodiment; FIG. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the embodiment. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the embodiment. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the embodiment. 4 is a schematic diagram showing a flow of an operation example of the ophthalmologic apparatus according to the embodiment; FIG. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the embodiment. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the embodiment. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the modification of the embodiment.

Exemplary embodiments of an ophthalmologic apparatus and an ophthalmologic information processing program according to the present invention will be described in detail with reference to the drawings. It should be noted that the descriptions of the documents cited in this specification and any known techniques can be incorporated into the following embodiments.

An ophthalmologic apparatus according to an embodiment has the function of an ophthalmologic information processing apparatus. The functions of the ophthalmologic information processing apparatus are implemented by a computer that executes processing according to an ophthalmologic information processing program. The ophthalmologic information processing apparatus includes a processor and a storage unit in which an ophthalmologic information processing program is stored in advance. Realize the function.

The ophthalmologic apparatus according to the embodiment can perform refractive power measurement (Ref measurement), and measurement and imaging using Optical Coherence Tomography (OCT).

Hereinafter, in the embodiments, the case where the swept source type OCT method is used in the measurement using OCT will be described in detail. It is also possible to apply the configuration according to the embodiment.

The ophthalmologic apparatus according to some embodiments further includes a subjective test optical system for performing subjective tests and an objective measurement system for performing other objective measurements.

Subjective testing is a measurement technique that uses responses from subjects to obtain information. The subjective examination includes subjective refraction measurement such as distance examination, near examination, contrast examination, glare examination, and visual field examination.

Objective measurement is a measurement technique that obtains information about the subject's eye using mainly physical techniques without referring to responses from the subject. Objective measurement includes measurement for acquiring characteristics of the eye to be inspected and photographing for acquiring an image of the eye to be inspected. Other objective measurements include keratometry, tonometry, fundus photography, and the like.

Hereinafter, the fundus conjugate position is a position that is substantially optically conjugate with the fundus of the subject's eye after alignment is completed, and means a position that is optically conjugate with the fundus of the subject's eye or its vicinity. Similarly, the pupil conjugate position is a position that is approximately optically conjugate with the pupil of the eye to be inspected in a state in which alignment is completed, and means a position that is optically conjugate with the pupil of the eye to be inspected or in the vicinity thereof. .

The ophthalmologic apparatus according to the embodiment generates abnormality degree information representing the degree of abnormality of the fundus based on a predetermined interlayer distance in the fundus obtained using OCT and standard data (normal eye data). The ophthalmologic apparatus displays the measured value of the refractive power of the subject's eye obtained by the refractive power measurement and the generated abnormality degree information on the same screen of the display means. An ophthalmologic apparatus according to some embodiments uses OCT to identify edema in the fundus (e.g., macula), corrects the refractive power measurement value of the subject eye according to the identified edema form, and corrects The measured value obtained is displayed on the display means. In some embodiments, when the morphology of the fundus oculi is observed in detail based on the above information on the degree of abnormality, the corrected measurement values are displayed on the display means. In some embodiments, the measured value of the refractive power of the subject's eye obtained by the refractive power measurement and the corrected measured value are displayed on the same screen of the display means.

<Configuration of optical system>
FIG. 1 shows a configuration example of an optical system of an ophthalmologic apparatus according to an embodiment. An ophthalmologic apparatus 1000 according to an embodiment includes an optical system for observing an eye to be examined E, an optical system for examining the eye to be examined E, and a dichroic mirror for wavelength-separating the optical paths of these optical systems. An anterior segment observation system 5 is provided as an optical system for observing the eye E to be examined. An OCT optical system and a reflector measurement optical system (refractive power measurement optical system) are provided as an optical system for examining the eye E to be examined.

The ophthalmologic apparatus 1000 includes a Z alignment system 1, an XY alignment system 2, a keratometric measurement system 3, a fixation projection system 4, an anterior segment observation system 5, a reflector measurement projection system 6, a reflector measurement light receiving system 7, and an OCT optical system 8. including. In the following description, for example, the anterior ocular segment observation system 5 uses light of 940 nm to 1000 nm, the reflector measurement optical system (ref measurement projection system 6, reflector measurement light receiving system 7) uses light of 830 nm to 880 nm, and the fixation projection system 4 uses light of 400 nm to 700 nm, and the OCT optical system 8 uses light of 1000 nm to 1100 nm.

(Anterior segment observation system 5)
The anterior segment observation system 5 captures a moving image of the anterior segment of the eye E to be examined. In the optical system passing through the anterior segment observation system 5, the imaging surface of the imaging element 59 is arranged at the pupil conjugate position. The anterior segment illumination light source 50 irradiates the anterior segment of the eye E to be examined with illumination light (for example, infrared light). The light reflected by the anterior segment of the subject's eye E passes through the objective lens 51, passes through the dichroic mirror 52, passes through a hole formed in the diaphragm (telecentric diaphragm) 53, and passes through the half mirror 23. , the relay lenses 55 and 56 and the dichroic mirror 76 . The dichroic mirror 52 synthesizes (separates) the optical path of the reflex measurement optical system and the optical path of the anterior eye observation system 5 . The dichroic mirror 52 is arranged such that the optical path synthesizing surface for synthesizing these optical paths is inclined with respect to the optical axis of the objective lens 51 . The light transmitted through the dichroic mirror 76 is imaged on the imaging surface of the imaging element 59 (area sensor) by the imaging lens 58 . The imaging element 59 performs imaging and signal output at a predetermined rate. The output (video signal) of the imaging device 59 is input to the processing section 9 which will be described later. The processing unit 9 displays an anterior segment image E' based on this video signal on a display screen 10a of the display unit 10, which will be described later. The anterior segment image E' is, for example, an infrared moving image.

(Z alignment system 1)
The Z alignment system 1 projects light (infrared light) onto the subject's eye E for alignment in the optical axis direction (front-rear direction, Z direction) of the anterior segment observation system 5 . The light output from the Z alignment light source 11 is projected onto the cornea Cr of the eye E to be examined, reflected by the cornea Cr, and imaged on the sensor surface of the line sensor 13 by the imaging lens 12 . When the position of the corneal vertex changes in the optical axis direction of the anterior segment observation system 5, the light projection position on the sensor surface of the line sensor 13 changes. The processing unit 9 obtains the position of the corneal vertex of the subject's eye E based on the light projection position on the sensor surface of the line sensor 13, and based on this, controls the mechanism for moving the optical system to perform Z alignment.

(XY alignment system 2)
The XY alignment system 2 applies light (infrared light) to the eye to be examined E for alignment in directions perpendicular to the optical axis of the anterior eye observation system 5 (horizontal direction (X direction) and vertical direction (Y direction)). to irradiate. The XY alignment system 2 includes an XY alignment light source 21 and a collimator lens 22 provided in an optical path branched from the optical path of the anterior eye observation system 5 by a half mirror 23 . Light output from the XY alignment light source 21 passes through the collimator lens 22 , is reflected by the half mirror 23 , and is projected onto the subject's eye E through the anterior eye observation system 5 . Reflected light from the cornea Cr of the eye E to be inspected is guided to the imaging device 59 through the anterior segment observation system 5 .

The image (bright point image) Br based on this reflected light is included in the anterior segment image E'. The processing unit 9 causes the display screen of the display unit to display the anterior segment image E′ including the bright spot image Br and the alignment mark AL. When manually performing the XY alignment, the user moves the optical system so as to guide the bright spot image Br into the alignment mark AL. When the alignment is performed automatically, the processing unit 9 controls the mechanism for moving the optical system so that the displacement of the bright spot image Br with respect to the alignment mark AL is cancelled.

(Kerato measurement system 3)
The keratometry system 3 projects a ring-shaped light beam (infrared light) for measuring the shape of the cornea Cr of the eye E to be examined onto the cornea Cr. The keratoplate 31 is arranged between the objective lens 51 and the eye E to be examined. A kerato ring light source 32 is provided on the back side of the kerato plate 31 (on the objective lens 51 side). By illuminating the kerat plate 31 with light from the keratizing light source 32, a ring-shaped light flux (arc-shaped or circumferential measurement pattern) is projected onto the cornea Cr of the eye E to be examined. Reflected light (keratling image) from the cornea Cr of the subject's eye E is detected by the imaging element 59 together with the anterior segment image E'. The processing unit 9 calculates corneal shape parameters representing the shape of the cornea Cr by performing known calculations based on this keratling image.

(ref measurement projection system 6, ref measurement light receiving system 7)
The ref measurement optical system includes a ref measurement projection system 6 and a ref measurement light receiving system 7 used for refractive power measurement. The ref measurement projection system 6 projects a refractive power measurement light beam (for example, a ring-shaped light beam) (infrared light) onto the fundus oculi Ef. The ref measurement light-receiving system 7 receives the return light from the subject's eye E of this luminous flux. The reflector measurement projection system 6 is provided on an optical path branched by a perforated prism 65 provided in the optical path of the reflector measurement light receiving system 7 . The aperture formed in the apertured prism 65 is arranged at the pupil conjugate position. In the optical system passing through the ref measurement light-receiving system 7, the imaging surface of the imaging device 59 is arranged at the fundus conjugate position.

In some embodiments, the ref measurement light source 61 is an SLD (Superluminescent Diode) light source, which is a high luminance light source. The ref measurement light source 61 is movable in the optical axis direction. A reflex measurement light source 61 is arranged at a fundus conjugate position. The light output from the ref measurement light source 61 passes through the relay lens 62 and enters the conical surface of the conical prism 63 . Light incident on the conical surface is deflected and emitted from the bottom surface of the conical prism 63 . Light emitted from the bottom surface of the conical prism 63 passes through a ring-shaped transparent portion of the ring aperture 64 . The light (ring-shaped luminous flux) that has passed through the transparent portion of the ring diaphragm 64 is reflected by the reflecting surface formed around the hole of the apertured prism 65, passes through the rotary prism 66, and is reflected by the dichroic mirror 67. be. The light reflected by the dichroic mirror 67 is reflected by the dichroic mirror 52, passes through the objective lens 51, and is projected onto the eye E to be examined. The rotary prism 66 is used for averaging the light quantity distribution of the ring-shaped light flux for blood vessels and diseased areas of the fundus oculi Ef and for reducing speckle noise caused by the light source.

The return light of the ring-shaped luminous flux projected onto the fundus oculi Ef passes through the objective lens 51 and is reflected by the dichroic mirrors 52 and 67 . The return light reflected by the dichroic mirror 67 passes through the rotary prism 66, passes through the aperture of the perforated prism 65, passes through the relay lens 71, is reflected by the reflecting mirror 72, and passes through the relay lens 73 and the focusing lens. Pass 74. The focusing lens 74 is movable along the optical axis of the ref measurement light receiving system 7 . The light that has passed through the focusing lens 74 is reflected by the reflecting mirror 75 , reflected by the dichroic mirror 76 , and imaged on the imaging surface of the imaging element 59 by the imaging lens 58 . The processing unit 9 calculates the refractive power value of the subject's eye E by performing a known calculation based on the output from the imaging device 59 . For example, power values include spherical power, cylinder power and cylinder axis angle, or equivalent spherical power.

(Fixation projection system 4)
An OCT optical system 8, which will be described later, is provided in an optical path separated by a dichroic mirror 67 from the optical path of the reflective measurement optical system. A fixation projection system 4 is provided on an optical path branched from the optical path of the OCT optical system 8 by a dichroic mirror 83 .

A fixation projection system 4 presents a fixation target to the eye E to be examined. A fixation unit 40 is arranged in the optical path of the fixation projection system 4 . The fixation unit 40 can move along the optical path of the fixation projection system 4 under the control of the processing section 9 which will be described later. The fixation unit 40 includes a liquid crystal panel 41 .

The liquid crystal panel 41 controlled by the processing unit 9 displays a pattern representing the fixation target. By changing the display position of the pattern on the screen of the liquid crystal panel 41, the fixation position of the subject's eye E can be changed. The fixation position of the subject's eye E includes a position for acquiring an image centered on the macula of the fundus oculi Ef, a position for acquiring an image centered on the optic papilla, and a position between the macula and the optic papilla. There is a position for acquiring an image centered on the center of the fundus in between. It is possible to arbitrarily change the display position of the pattern representing the fixation target. Instead of the liquid crystal panel 41, a transmissive optotype chart in which optotypes or the like are printed on a film or the like and an illumination light source for illuminating the optotype chart may be provided.

Light from the liquid crystal panel 41 passes through the relay lens 42 , dichroic mirror 83 , relay lens 82 , reflection mirror 81 , dichroic mirror 67 , and dichroic mirror 52 . . The light reflected by the dichroic mirror 52 passes through the objective lens 51 and is projected onto the fundus oculi Ef. In some embodiments, each of the liquid crystal panel 41 and the relay lens 42 is independently movable in the optical axis direction.

(OCT optical system 8)
The OCT optical system 8 is an optical system for performing OCT measurement. The position of the focusing lens 87 is adjusted so that the end surface of the optical fiber f1 is conjugated to the imaging site (fundus oculi Ef or anterior segment) and the optical system based on the results of the reflex measurement performed prior to the OCT measurement. .

The OCT optical system 8 is provided in an optical path separated by a dichroic mirror 67 from the optical path of the ref measurement optical system. The optical path of the fixation projection system 4 is coupled to the optical path of the OCT optical system 8 by a dichroic mirror 83 . Thereby, the respective optical axes of the OCT optical system 8 and the fixation projection system 4 can be coaxially coupled.

OCT optical system 8 includes an OCT unit 100 . As shown in FIG. 2, in the OCT unit 100, the OCT light source 101 is a wavelength-swept (wavelength scanning) light source capable of sweeping (scanning) the wavelength of emitted light, similar to a general swept-source type OCT apparatus. Consists of A swept-wavelength light source includes a laser light source including a resonator. The OCT light source 101 temporally changes the output wavelength in the near-infrared wavelength band invisible to the human eye.

As illustrated in FIG. 2, the OCT unit 100 is provided with an optical system for performing swept-source OCT. This optical system includes an interference optical system. This interference optical system has a function of dividing light from a wavelength tunable light source (wavelength swept light source) into measurement light and reference light, return light of the measurement light from the subject's eye E, and reference light passing through the reference light path. and a function of generating interference light and a function of detecting this interference light. A detection result (detection signal) of the interference light obtained by the interference optical system is a signal indicating the spectrum of the interference light, and is sent to the processing unit 9 .

The OCT light source 101 includes, for example, a near-infrared tunable laser that changes the wavelength of emitted light (wavelength range of 1000 nm to 1100 nm) at high speed. The light L0 output from the OCT light source 101 is guided to the polarization controller 103 by the optical fiber 102, and its polarization state is adjusted. The light L0 whose polarization state has been adjusted is guided by the optical fiber 104 to the fiber coupler 105 and split into the measurement light LS and the reference light LR.

The reference light LR is guided by the optical fiber 110 to the collimator 111 and converted into a parallel beam, and guided to the corner cube 114 via the optical path length correction member 112 and the dispersion compensation member 113 . The optical path length correction member 112 acts to match the optical path length of the reference light LR and the optical path length of the measurement light LS. The dispersion compensation member 113 acts to match the dispersion characteristics between the reference light LR and the measurement light LS. The corner cube 114 is movable in the incident direction of the reference light LR, thereby changing the optical path length of the reference light LR.

The reference light LR that has passed through the corner cube 114 passes through the dispersion compensating member 113 and the optical path length correcting member 112 , is converted by the collimator 116 from a parallel beam to a converged beam, and enters the optical fiber 117 . The reference light LR incident on the optical fiber 117 is guided to the polarization controller 118 to adjust its polarization state, guided to the attenuator 120 by the optical fiber 119 to adjust the light amount, and guided to the fiber coupler 122 by the optical fiber 121.

On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the optical fiber f1, converted into a parallel light beam by the collimator lens unit 89, and passes through the light scanner 88, the focusing lens 87, the relay lens 85, and the reflecting mirror 84. , and is reflected by the dichroic mirror 83 .

The light scanner 88 deflects the measurement light LS one-dimensionally or two-dimensionally. Optical scanner 88 includes, for example, a first galvanometer mirror and a second galvanometer mirror. The first galvanomirror deflects the measurement light LS so as to scan the imaging region (fundus oculi Ef or anterior segment) in the horizontal direction perpendicular to the optical axis of the OCT optical system 8 . The second galvanomirror deflects the measurement light LS deflected by the first galvanomirror so as to scan the imaging region in the vertical direction perpendicular to the optical axis of the OCT optical system 8 . Scanning modes of the measurement light LS by the light scanner 88 include, for example, horizontal scanning, vertical scanning, cross scanning, radial scanning, circular scanning, concentric scanning, and spiral scanning.

The measurement light LS reflected by the dichroic mirror 83 passes through the relay lens 82, is reflected by the reflecting mirror 81, passes through the dichroic mirror 67, is reflected by the dichroic mirror 52, is refracted by the objective lens 51, and reaches the subject's eye E incident on The measurement light LS is scattered and reflected at various depth positions of the eye E to be examined. The return light of the measurement light LS from the subject's eye E travels in the opposite direction along the same path as the forward path, is guided to the fiber coupler 105 , and reaches the fiber coupler 122 via the optical fiber 128 .

The fiber coupler 122 combines (interferences) the measurement light LS that has entered via the optical fiber 128 and the reference light LR that has entered via the optical fiber 121 to generate interference light. The fiber coupler 122 generates a pair of interference lights LC by splitting the interference lights at a predetermined splitting ratio (for example, 1:1). A pair of interference beams LC are guided to detector 125 through optical fibers 123 and 124, respectively.

Detector 125 is, for example, a balanced photodiode. A balanced photodiode includes a pair of photodetectors that respectively detect a pair of interference lights LC, and outputs a difference between a pair of detection results obtained by these photodetectors. The detector 125 sends this output (detection signal) to a DAQ (Data Acquisition System) 130 .

A clock KC is supplied from the OCT light source 101 to the DAQ 130 . The clock KC is generated in the OCT light source 101 in synchronization with the output timing of each wavelength swept within a predetermined wavelength range by the wavelength tunable light source. The OCT light source 101, for example, optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then outputs the clock KC based on the result of detecting these combined lights. Generate. The DAQ 130 samples the detection signal input from the detector 125 based on the clock KC. The DAQ 130 sends the sampling result of the detection signal from the detector 125 to the arithmetic processing section 220 of the processing section 9 . For example, for each series of wavelength scans (for each A line), the arithmetic processing unit 220 forms a reflection intensity profile for each A line by applying Fourier transform or the like to the spectral distribution based on the sampling data. Furthermore, the arithmetic processing unit 220 forms image data by imaging the reflection intensity profile of each A line.

In this example, a corner cube 114 is provided for changing the length of the optical path (reference optical path, reference arm) of the reference light LR. It is also possible to change the difference between

The processing unit 9 calculates a refractive power value from the measurement result obtained using the reflector measurement optical system, and based on the calculated refractive power value, the fundus oculi Ef, the reflector measurement light source 61, and the image sensor 59 are conjugated. The ref measurement light source 61 and the focusing lens 74 are moved in the optical axis direction to the respective positions. In some embodiments, the processing unit 9 moves the focusing lens 87 of the OCT optical system 8 along its optical axis in conjunction with the movement of the focusing lens 74 . In some embodiments, the processing section 9 moves the liquid crystal panel 41 (fixation unit 40) along its optical axis in conjunction with the movement of the ref measurement light source 61 and the focusing lens 74. FIG.

<Configuration of processing system>
The configuration of the processing system of the ophthalmologic apparatus 1000 will be described. An example of the functional configuration of the processing system of the ophthalmologic apparatus 1000 is shown in FIGS. 3 and 4. FIG. FIG. 3 shows an example of a functional block diagram of the processing system of the ophthalmologic apparatus 1000. As shown in FIG. FIG. 4 shows an example of a functional block diagram of the data processing unit 223. As shown in FIG.

The processing unit 9 controls each unit of the ophthalmologic apparatus 1000 . In addition, the processing unit 9 can execute various arithmetic processing. The processing unit 9 includes a processor.プロセッサの機能は、例えば、ＣＰＵ（Ｃｅｎｔｒａｌ Ｐｒｏｃｅｓｓｉｎｇ Ｕｎｉｔ）、ＧＰＵ（Ｇｒａｐｈｉｃｓ Ｐｒｏｃｅｓｓｉｎｇ Ｕｎｉｔ）、ＡＳＩＣ（Ａｐｐｌｉｃａｔｉｏｎ Ｓｐｅｃｉｆｉｃ Ｉｎｔｅｇｒａｔｅｄ Ｃｉｒｃｕｉｔ）、プログラマブル論理デバイス（例えば、ＳＰＬＤ（Ｓｉｍｐｌｅ Ｐｒｏｇｒａｍｍａｂｌｅ Ｌｏｇｉｃ Ｄｅｖｉｃｅ）、ＣＰＬＤ（Ｃｏｍｐｌｅｘ Ｐｒｏｇｒａｍｍａｂｌｅ Ｌｏｇｉｃ Ｄｅｖｉｃｅ） , FPGA (Field Programmable Gate Array)). The processing unit 9 implements the functions according to the embodiment by, for example, reading and executing a program stored in a storage circuit or storage device.

The processing unit 9 is an example of an "ophthalmic information processing apparatus" according to the embodiment. That is, the program for realizing the function of the processing unit 9 is an example of the "ophthalmic information processing program" according to the embodiment.

Processing unit 9 includes control unit 210 and arithmetic processing unit 220 . The ophthalmologic apparatus 1000 also includes a moving mechanism 200 , a display section 270 , an operation section 280 and a communication section 290 .

The moving mechanism 200 includes a Z alignment system 1, an XY alignment system 2, a keratometric measurement system 3, a fixation projection system 4, an anterior segment observation system 5, a reflector measurement projection system 6, a reflector measurement light receiving system 7, an OCT optical system 8, and the like. This is a mechanism for moving the head section in which the optical system is housed in the front, rear, left, and right directions. For example, the moving mechanism 200 is provided with an actuator that generates driving force for moving the head section and a transmission mechanism that transmits this driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is configured by, for example, a combination of gears, a rack and pinion, or the like. The control unit 210 (main control unit 211) controls the movement mechanism 200 by sending control signals to the actuators.

(control unit 210)
The control unit 210 includes a processor and controls each unit of the ophthalmologic apparatus. Control unit 210 includes a main control unit 211 and a storage unit 212 . A computer program for controlling the ophthalmologic apparatus is stored in advance in the storage unit 212 . The computer programs include a light source control program, a detector control program, an optical scanner control program, an optical system control program, an arithmetic processing program, a user interface program, and the like. The main control unit 211 operates according to such a computer program, so that the control unit 210 executes control processing.

A main control unit 211 performs various controls of the ophthalmologic apparatus as a measurement control unit. Control of the Z alignment system 1 includes control of the Z alignment light source 11, control of the line sensor 13, and the like. The control of the Z alignment light source 11 includes turning on/off the light source, adjusting the amount of light, and adjusting the aperture. Control of the line sensor 13 includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection element. As a result, the Z alignment light source 11 is switched between lighting and non-lighting, or the amount of light is changed. The main control unit 211 captures the signal detected by the line sensor 13 and identifies the projection position of the light on the line sensor 13 based on the captured signal. The main control unit 211 obtains the position of the corneal vertex of the subject's eye E based on the specified projection position, and based on this, controls the movement mechanism 200 to move the head unit in the front-rear direction (Z alignment).

Control of the XY alignment system 2 includes control of the XY alignment light source 21 and the like. The control of the XY alignment light source 21 includes turning on/off the light source, adjusting the amount of light, and adjusting the aperture. Thereby, lighting and non-lighting of the XY alignment light source 21 are switched, or the amount of light is changed. The main control unit 211 captures the signal detected by the imaging element 59 and identifies the position of the bright spot image based on the return light from the XY alignment light source 21 based on the captured signal. The main control unit 211 controls the moving mechanism 200 so as to cancel the displacement of the position of the bright point image Br with respect to a predetermined target position (for example, the center position of the alignment mark AL), and moves the head unit in left, right, up and down directions. Move (XY alignment).

Control of the keratometry system 3 includes control of the keratometry light source 32 and the like. The control of the keratling light source 32 includes turning on/off the light source, adjusting the amount of light, and adjusting the aperture. Thereby, lighting and non-lighting of the keratling light source 32 are switched, or the amount of light is changed. The main control unit 211 causes the arithmetic processing unit 220 to perform a known arithmetic operation on the keratling image detected by the imaging device 59 . Thereby, the corneal shape parameter of the eye E to be examined is obtained.

The control of the fixation projection system 4 includes control of the liquid crystal panel 41, movement control of the fixation unit 40, and the like. The control of the liquid crystal panel 41 includes turning on/off the display of the fixation target, switching the display position of the fixation target, and the like.

For example, the fixation projection system 4 is provided with a moving mechanism that moves the liquid crystal panel 41 (or the fixation unit 40) in the optical axis direction. Similar to the moving mechanism 200, this moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the movement mechanism by sending control signals to the actuators, and moves at least the liquid crystal panel 41 in the optical axis direction. Thereby, the position of the liquid crystal panel 41 is adjusted so that the liquid crystal panel 41 and the fundus oculi Ef are optically conjugated.

The control of the anterior segment observation system 5 includes control of the anterior segment illumination light source 50, control of the imaging element 59, and the like. The control of the anterior ocular segment illumination light source 50 includes turning on/off the light source, light amount adjustment, aperture adjustment, and the like. As a result, the lighting and non-lighting of the anterior segment illumination light source 50 is switched, or the amount of light is changed. Control of the imaging element 59 includes exposure adjustment, gain adjustment, detection rate adjustment, and the like of the imaging element 59 . The main control unit 211 captures the signals detected by the imaging device 59 and causes the arithmetic processing unit 220 to execute processing such as formation of an image based on the captured signals.

The control of the ref measurement projection system 6 includes control of the ref measurement light source 61, control of the rotary prism 66, and the like. The control of the ref measurement light source 61 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. As a result, lighting and non-lighting of the ref measurement light source 61 are switched, or the amount of light is changed. For example, the reflector measurement projection system 6 includes a moving mechanism that moves the reflector measurement light source 61 in the optical axis direction. Similar to the moving mechanism 200, this moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the movement mechanism by sending a control signal to the actuator to move the ref measurement light source 61 in the optical axis direction. The control of the rotary prism 66 includes rotation control of the rotary prism 66 and the like. For example, a rotating mechanism for rotating the rotary prism 66 is provided, and the main controller 211 rotates the rotary prism 66 by controlling this rotating mechanism.

Control of the ref measurement light-receiving system 7 includes control of the focusing lens 74 and the like. Control of the focusing lens 74 includes movement control of the focusing lens 74 in the optical axis direction. For example, the ref measurement light-receiving system 7 includes a moving mechanism that moves the focusing lens 74 in the optical axis direction. Similar to the moving mechanism 200, this moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator to move the focusing lens 74 in the optical axis direction. The main control unit 211 controls the refractometer measurement light source 61 and the focusing lens 74 according to the refractive power of the subject's eye E, for example, so that the refractometer light source 61, the fundus oculi Ef, and the imaging device 59 are optically conjugate. Axial movement is possible.

Control of the OCT optical system 8 includes control of the OCT light source 101, control of the optical scanner 88, control of the focusing lens 87, control of the corner cube 114, control of the detector 125, control of the DAQ 130, and the like. The control of the OCT light source 101 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. Control of the optical scanner 88 includes control of the scanning position, scanning range, and scanning speed by the first galvanomirror, and control of the scanning position, scanning range, and scanning speed by the second galvanomirror.

The control of the focusing lens 87 includes movement control of the focusing lens 87 in the optical axis direction, movement control of the focusing lens 87 to the focus reference position corresponding to the imaging part, movement range (focusing) corresponding to the imaging part. movement control within the focal range). For example, the OCT optical system 8 includes a moving mechanism that moves the focusing lens 87 in the optical axis direction. Similar to the moving mechanism 200, this moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator to move the focusing lens 87 in the optical axis direction. In some embodiments, the ophthalmic device is provided with a retaining member that retains the focusing lenses 74 and 87 and a drive that drives the retaining member. The main control section 211 performs movement control of the focusing lenses 74 and 87 by controlling the driving section. For example, the main control unit 211 may move only the focusing lens 87 based on the intensity of the interference signal after moving the focusing lens 87 in conjunction with the movement of the focusing lens 74 .

The control of the corner cube 114 includes movement control of the corner cube 114 along the optical path. For example, the OCT optical system 8 includes a moving mechanism that moves the corner cube 114 along the optical path. Similar to the moving mechanism 200, this moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits this driving force. The main control unit 211 controls the moving mechanism by sending control signals to the actuators to move the corner cube 114 along the optical path. Control of the detector 125 includes exposure adjustment, gain adjustment, and detection rate adjustment of the detection element. The main control unit 211 samples the signal detected by the detector 125 by the DAQ 130, and causes the arithmetic processing unit 220 (image forming unit 222) to perform processing such as formation of an image based on the sampled signal.

Further, the main control unit 211 functions as a display control unit to display the refractive power measurement value calculated by the eye refractive power calculation unit 221, the tomographic image formed by the image forming unit 222, and the processing result of the data processing unit 223, which will be described later. The corresponding information is displayed on the display unit 270 . As the processing result of the data processing unit 223, the intraocular distance calculated by the intraocular distance calculation unit 231, the abnormality degree information generated by the analysis unit 232, the refractive power measurement value corrected by the measurement value correction unit 233, etc. be.

Furthermore, the main control unit 211 performs processing of writing data to the storage unit 212 and processing of reading data from the storage unit 212 .

(storage unit 212)
The storage unit 212 stores various data. The data stored in the storage unit 212 includes, for example, objective measurement results, OCT measurement results, tomographic image data, anterior segment image data, eye information, standard data, and the like. The eye information to be inspected includes information related to the eye to be inspected, such as left eye/right eye identification information.

Standard data is statistically derived from measurement data of a large number of normal eyes, and is called normal eye data (normative data) or the like. The standard data includes the intraocular distance in normal eyes and the predetermined interlayer distance of the fundus. The intraocular distance includes axial length (distance from the apex of the cornea to the inner limiting membrane), corneal thickness, anterior chamber depth, lens thickness, vitreous cavity length, retinal thickness, and choroidal thickness. The predetermined interlayer distance of the fundus includes the macular retinal thickness (Retinal Thickness), the inner limiting membrane (Inner Limiting Membrane), the nerve fiber layer, the ganglion cell layer, the inner reticular layer, the inner nuclear layer, the outer reticular layer, the outer The distance between any two layers such as the granular layer, the outer limiting membrane, the photoreceptor layer, the retinal pigment epithelium layer, and the like. The macular retinal thickness is the distance between the inner limiting membrane and the retinal pigment epithelium layer in the macula (eg, a position within a predetermined range from the fovea centralis).

The storage unit 212 also stores various programs and data for operating the ophthalmologic apparatus.

(Arithmetic processing unit 220)
The arithmetic processing unit 220 includes an eye refractive power calculation unit 221 , an image forming unit 222 and a data processing unit 223 .

(Eye refractive power calculator 221)
The eye refractive power calculation unit 221 calculates a ring image (pattern image ). For example, the eye refractive power calculator 221 obtains the barycentric position of the ring image from the luminance distribution in the obtained image in which the ring image is rendered, and obtains the luminance distribution along a plurality of scanning directions radially extending from this barycentric position. , the ring image is specified from this luminance distribution. Subsequently, the eye refractive power calculation unit 221 obtains an approximate ellipse of the specified ring image, and substitutes the major axis and minor axis of the approximate ellipse into a known formula to obtain the spherical power, the cylinder power, and the cylinder axis angle (refraction strength value). Alternatively, the eye refractive power calculator 221 can obtain parameters of the eye refractive power based on deformation and displacement of the ring image with respect to the reference pattern.

Based on the difference between the wavelength region of light (near-infrared light) projected onto the fundus oculi Ef by the reflex measurement projection system 6 and the wavelength region of light (visible light) used in the subjective examination, the eye refractive power calculator 221 A refractive power value (a measurement of refractive power) can be determined. In subjective examinations, visible light is perceived near the retinal surface (specifically, the inner limiting membrane), and the orientation of the Landolt's ring, for example, is recognized, but in refractive power measurement, the light from the retinal pigment epithelium layer is recognized. Reflected light is detected. Let α be the refractive power from the cornea to the inner limiting membrane, β be the refractive power from the cornea to the retinal pigment epithelium layer, and γ be the correction value corresponding to the difference in the above wavelength regions. On the other hand, the correction value γ is obtained so that (α−β−γ), which represents the difference between the measured value of refractive power and the test value of the subjective test, becomes zero. The eye refractive power calculator 221 obtains the measured value of the refractive power of the subject's eye E by adding the correction value γ to the refractive power value obtained as described above.

The eye refractive power calculator 221 also calculates the corneal refractive power, the corneal astigmatism degree, and the corneal astigmatism axis angle based on the keratling image acquired by the anterior eye observation system 5 . For example, the eye refractive power calculator 221 calculates the corneal curvature radii of the strong and weak principal meridians of the corneal front surface by analyzing the keratling image, and calculates the above parameters based on the corneal curvature radii.

(Image forming unit 222)
The image forming unit 222 forms image data of a tomographic image of the fundus oculi Ef based on the signal detected by the detector 115 . That is, the image forming unit 222 forms image data of the subject's eye E based on the detection result of the interference light LC by the interference optical system. This processing includes processing such as filter processing and FFT (Fast Fourier Transform), as in conventional spectral domain type OCT. The image data acquired in this manner is a data set containing a group of image data formed by imaging reflection intensity profiles in a plurality of A-lines (paths of each measuring light LS in the eye E to be examined). be.

To improve image quality, multiple data sets collected by scanning the same pattern multiple times can be superimposed (averaged).

(Data processing unit 223)
The data processing unit 223 performs various data processing (image processing) and analysis processing on the tomogram formed by the image forming unit 222 . For example, the data processing unit 223 executes correction processing such as image luminance correction and dispersion correction. In addition, the data processing unit 223 performs various image processing and analysis processing on the image (anterior segment image, etc.) obtained using the anterior segment observation system 5 .

The data processing unit 223 can form volume data (voxel data) of the subject's eye E by executing known image processing such as interpolation processing for interpolating pixels between tomographic images. When displaying an image based on volume data, the data processing unit 223 performs rendering processing on this volume data to form a pseudo-three-dimensional image when viewed from a specific line-of-sight direction.

The data processor 223 includes an intraocular distance calculator 231 , an analyzer 232 , and a measured value corrector 233 .

(Intraocular distance calculator 231)
The intraocular distance calculator 231 obtains one or more intraocular distances in the subject's eye E based on the detection result of the interference light LC obtained by the OCT optical system 8 . The one or more intraocular distances include the axial length of the eye (the distance from the corneal vertex to the internal limiting membrane). In some embodiments, the intraocular distance calculator 231 obtains one or more intraocular distances based on data obtained by 3D scanning with the OCT optical system 8 . In some embodiments, the intraocular distance calculator 231 analyzes the detection result of the interference light LC obtained by the OCT optical system 8 to obtain the detection result of the interference light corresponding to the predetermined site in the eye (interference signal ) are identified, and the intraocular distance is obtained based on the distance between the identified peak positions. The intraocular distance calculator 231 according to some embodiments further determines corneal thickness, anterior chamber depth, lens thickness, vitreous cavity length, retinal thickness, choroidal thickness, and the like.

(analysis unit 232)
The analysis unit 232 obtains a predetermined interlayer distance in the fundus based on the detection result of the interference light LC obtained by the OCT optical system 8, and determines the degree of abnormality of the fundus based on the obtained interlayer distance and the standard data. Generate degree information. The analysis unit 232 includes a layer area identification unit 232A, an edema identification unit 232B, a layer thickness calculation unit 232C, a comparison unit 232D, and an abnormality degree information generation unit 232E.

(Layer area specifying unit 232A)
The layer region specifying unit 232A specifies a layer region corresponding to a predetermined layer tissue of the fundus oculi Ef based on the detection result of the interference light LC obtained by the OCT optical system 8 . In some embodiments, the layer region identifying unit 232A identifies a layer region corresponding to a predetermined layer tissue of the fundus oculi Ef by analyzing three-dimensional data collected by 3D scanning with the OCT optical system 8. In some embodiments, the layer region specifying unit 232A performs segmentation processing on the tomographic image of the fundus oculi Ef formed by the image forming unit 222 based on the detection result of the interference light LC obtained by the OCT optical system 8. A layer region corresponding to a predetermined layer structure is specified by applying the coating. Segmentation is generally performed based on luminance values of OCT images (2D tomograms, 3D images, etc.). Each layer structure of the fundus oculi Ef has a characteristic reflectance, and the image area of the layer structure also has a characteristic brightness value. In segmentation, target image regions are identified based on such characteristic luminance values.

The layer region specifying unit 232A includes the inner limiting membrane, the nerve fiber layer, the ganglion cell layer, the inner plexiform layer, the inner nuclear layer, the outer plexiform layer, the outer nuclear layer, the outer limiting membrane, the photoreceptor layer, and the retina. It is possible to specify the pigment epithelial layer (Retinal Pigment Epithelium).

(Edema identification unit 232B)
The edema identifying unit 232B identifies edema in the fundus oculi Ef (in particular, the macula) based on the detection result of the interference light LC obtained by the OCT optical system 8. The edema identification unit 232B can identify the position and form (outline, shape) of edema in the fundus oculi Ef. The edema identification unit 232B identifies edema in the fundus oculi Ef based on the detection result of the interference light LC obtained by the OCT optical system 8. The edema identifying unit 232B can identify edema based on the distance between the inner limiting membrane and the retinal pigment epithelium layer identified by the layer region identifying unit 232A. In some embodiments, the edema identifier 232B identifies edema based on the change in distance in the B-scan direction between the inner limiting membrane and the retinal pigment epithelium layer identified by the layer area identifier 232A. In some embodiments, the edema identifying unit 232B identifies edema in the fundus oculi Ef by analyzing three-dimensional data collected by 3D scanning with the OCT optical system 8. In some embodiments, the edema identifying unit 232B performs segmentation processing on the tomographic image of the fundus oculi Ef formed by the image forming unit 222 based on the detection result of the interference light LC obtained by the OCT optical system 8. to identify edema.

(Layer thickness calculator 232C)
The layer thickness calculator 232C calculates the thickness (interlayer distance) of the layer region identified by the layer region identifier 232A. The layer thickness calculator 232C can calculate thicknesses at a plurality of positions in the layer region identified by the layer region identifier 232A and output statistical values (average value, median value, etc.) of these. The thickness of the layer region is measured, for example, as the distance between the upper surface (surface on the fundus surface side) and the lower surface (surface on the deep fundus side) of the layer region. This distance is measured, for example, along the Z direction.

The layer thickness calculator 232C can obtain at least the retinal thickness of the macular region and the height of edema in the macular region. The retinal thickness of the macula and the height of edema in the macula are obtained from the A-scan results at a representative position in the macula, or as the average value of the values obtained from the A-scan results at two or more positions in the macula. or

(Comparator 232D)
The comparison unit 232D compares the thickness of the layer region calculated by the layer thickness calculation unit 232C with the standard data stored in the storage unit 212. FIG. Further, when the standard data includes the thickness of the layer region at a plurality of positions in the eye, the comparison unit 232D stores the thickness of the layer region calculated by the layer thickness calculation unit 232C for each position in the storage unit 212. It is possible to compare the data with standard data stored therein, and store the comparison result in the storage unit 212 in association with each position.

(Abnormality degree information generation unit 232E)
The abnormality degree information generation unit 232E generates a retinal index (abnormality degree information) representing the degree of abnormality of the retina (fundus) based on the comparison result obtained by the comparison unit 232D. The retinal index is information indicating whether there is no retinal abnormality, whether there is retinal abnormality, or the degree of retinal abnormality.

FIG. 5 schematically shows an example of a retina index according to the embodiment.

The degree-of-abnormality information generator 232E calculates a retina index according to the difference between the standard data and the thickness of the layer region calculated by the layer thickness calculator 232C. When the difference between the standard data and the calculated macular retinal thickness is equal to or less than a predetermined threshold value, the abnormality degree information generation unit 232E outputs "10" representing that there is no abnormality in the retina as the retinal index. When the difference between the standard data and the calculated macular retinal thickness is greater than a predetermined threshold value, the abnormality degree information generation unit 232E sets any one of "1" to "9" indicating that there is an abnormality in the retina as a retinal index. output as The degree-of-abnormality information generation unit 232E can output the retinal index so that the numerical value decreases stepwise as the difference between the standard data and the calculated macular retinal thickness increases.

(Measurement value correction unit 233)
The measured value correction unit 233 corrects the measured value of the refractive power of the subject's eye E calculated by the eye refractive power calculation unit 221 according to the form of edema identified by the edema identification unit 232B. Specifically, the measured value correction unit 233 corrects the measured value of the refractive power of the subject's eye E calculated by the eye refractive power calculation unit 221 according to the height of edema in the macular region. In some embodiments, when edema is identified by the edema identifying unit 232B, the measured value correction unit 233 corrects the measured value of the refractive power of the subject's eye E according to the height of the identified edema.

6A and 6B are diagrams for explaining the operation of the measured value corrector 233 according to the embodiment. FIG. 6A is an explanatory diagram of the refractive power value of the subject's eye E calculated by the eye refractive power calculator 221. FIG. FIG. 6B is an explanatory diagram of the correction value of the refractive power value of the subject's eye E corrected by the measurement value correction unit 233 . 6A and 6 schematically show the tomographic structure of the fundus oculi Ef.

As described above, the eye refractive power calculator 221 obtains the refractive power value based on the near-infrared light reflected by the retinal pigment epithelium layer RPE. Since the subjective test value is obtained by recognizing an image in which visible light is obtained near the internal limiting membrane ILM, the eye refractive power calculation unit 221 calculates the refractive power value obtained as described above by A value obtained by applying a correction value γ corresponding to the distance between the inner limiting membrane ILM and the retinal pigment epithelium layer RPE (macular retinal thickness RT) is output as a measured refractive power value.

On the other hand, the measurement value correction unit 233 further applies a correction value γ1 corresponding to the height of edema in the macular region to the measurement value obtained by applying the correction value γ as shown in FIG. 6A. .

Specifically, as shown in FIG. 6B, the measured value correction unit 233 corrects the above measured values in consideration of the edema height MET in the macular region. AL _ILM is the axial length, which is the distance from the corneal vertex to the inner limiting membrane, RT is the macular retinal thickness, MET is the edema height in the macula, and n is the intraocular equivalent refractive index. Then, the correction value γ1 is represented by the following formula.

The correction value γ1 may be determined from the measured value as shown in Equation (1), or may be determined using a constant value const or a function of refractive power. In some embodiments, the constant value const is represented by the following formula.

In this case, the correction value γ1 is represented by the following formula.

The measured value correction unit 233 adds the correction value γ1 shown in the formula (1) or (3) to the measured value of the refractive power obtained by the eye refractive power calculation unit 221, thereby calculating the refractive power of the eye E to be examined. Correct the measured value.

(Display unit 270, operation unit 280)
Display unit 270 displays information as a user interface unit under the control of control unit 210 . Display unit 270 includes display unit 10 shown in FIG. 1 and the like.

The operation unit 280 is used as a user interface unit to operate the ophthalmologic apparatus. The operation unit 280 includes various hardware keys (joystick, button, switch, etc.) provided in the ophthalmologic apparatus. The operation unit 280 may also include various software keys (buttons, icons, menus, etc.) displayed on the touch panel display screen 10a.

At least part of the display unit 270 and the operation unit 280 may be configured integrally. A typical example is a touch panel display screen 10a.

(Communication unit 290)
The communication unit 290 has a function for communicating with an external device (not shown). The communication unit 290 has a communication interface according to a connection form with an external device. An example of an external device is a spectacle lens measuring device for measuring the optical properties of lenses. The spectacle lens measuring device measures the dioptric power of the spectacle lens worn by the subject, and inputs this measurement data to the ophthalmologic device 1000 . Also, the external device may be any ophthalmologic device, a device (reader) that reads information from a recording medium, or a device (writer) that writes information to a recording medium. Furthermore, the external device may be a hospital information system (HIS) server, a DICOM (Digital Imaging and Communication in Medicine) server, a doctor terminal, a mobile terminal, a personal terminal, a cloud server, or the like. The communication unit 290 may be provided in the processing unit 9, for example.

The ref measurement optical system (the ref measurement projection system 6 and the ref measurement light receiving system 7) and the eye refractive power calculator 221 are examples of the "refractive power measurement section" according to the embodiment. The OCT optical system 8 is an example of a "data acquisition section" according to the embodiment. The control unit 210 (main control unit 211) is an example of a "display control unit".

<Operation example>
The operation of the ophthalmologic apparatus 1000 according to the embodiment will be described.

FIG. 7 shows an example of the operation of the ophthalmologic apparatus 1000. As shown in FIG. FIG. 7 depicts a flow diagram of an example operation of the ophthalmic device 1000 . A computer program for realizing the processing shown in FIG. 7 is stored in the storage unit 212 . The main control unit 211 executes the processing shown in FIG. 7 by operating according to this computer program. Here, it is assumed that subject information is stored in the storage unit 212 in advance.

(S1: Alignment)
The ophthalmologic apparatus 1000 performs alignment when the examiner performs a predetermined operation on the operation unit 280 while the subject's face is fixed to a face receiving unit (not shown).

Specifically, the main controller 211 turns on the Z alignment light source 11 and the XY alignment light source 21 . Further, the main controller 211 turns on the anterior segment illumination light source 50 . The processing unit 9 acquires the imaging signal of the anterior segment image on the imaging surface of the imaging element 59 and causes the display unit 270 to display the anterior segment image. After that, the optical system shown in FIG. 1 is moved to the examination position of the eye E to be examined. The inspection position is a position at which the eye to be inspected E can be inspected with sufficient accuracy. The subject's eye E is placed at the inspection position through the above-described alignment (alignment by the Z alignment system 1, the XY alignment system 2, and the anterior segment observation system 5). Movement of the optical system is executed by the control unit 210 according to an operation or instruction by the user or an instruction by the control unit 210 . That is, the movement of the optical system to the inspection position of the subject's eye E and the preparation for objective measurement are performed.

Further, the main control unit 211 moves the ref measurement light source 61, the focusing lens 74, and the fixation unit 40 (liquid crystal panel 41) to their origin positions (for example, positions corresponding to 0D) along their respective optical axes. move.

Note that the keratometry may be performed after the alignment in step S1 is completed. In this case, the main controller 211 causes the liquid crystal panel 41 to display a pattern indicating a fixation target at a display position corresponding to a desired fixation position. Thereby, the subject's eye E is gazed at the desired fixation position. After that, the main controller 211 turns on the keratling light source 32 . When light is emitted from the keratizing light source 32, a ring-shaped light beam for corneal shape measurement is projected onto the cornea Cr of the eye E to be examined. The eye refractive power calculator 221 calculates the corneal curvature radius by performing arithmetic processing on the image acquired by the imaging device 59, and calculates the corneal refractive power, the corneal astigmatism degree, and the corneal astigmatism from the calculated corneal curvature radius. Calculate the axis angle. In the control unit 210 , the calculated corneal refractive power and the like are stored in the storage unit 212 .

In response to an instruction from the main control unit 211 or a user's operation or instruction to the operation unit 280, the operation of the ophthalmologic apparatus 1000 proceeds to step S2.

(S2: refractive power measurement)
In the refractive power measurement, the main controller 211 projects the ring-shaped measurement pattern light beam for the refractive power measurement onto the eye E to be examined as described above. A ring image is formed on the imaging surface of the imaging device 59 based on the return light of the measurement pattern light flux from the eye E to be inspected. The main control unit 211 determines whether or not the ring image based on the return light from the fundus oculi Ef detected by the imaging element 59 has been acquired. For example, the main control unit 211 detects the position (pixel) of the edge of the image based on the return light detected by the imaging device 59, and determines whether the width of the image (difference between the outer diameter and the inner diameter) is equal to or greater than a predetermined value. determine whether or not Alternatively, the main control unit 211 determines whether a ring image can be obtained by determining whether a ring can be formed based on points (images) having a predetermined height (ring diameter) or more. good too.

When it is determined that the ring image has been acquired, the eye refractive power calculation unit 221 analyzes the ring image based on the return light of the measurement pattern light flux projected onto the subject's eye E by a known method, and calculates the temporary spherical power S and A temporary astigmatism power C is obtained. Based on the obtained temporary spherical power S and cylindrical power C, the main control unit 211 adjusts the ref measurement light source 61, the focusing lens 74, and the fixation unit 40 (liquid crystal panel 41) to the equivalent spherical power (S+C/2). position (position corresponding to the temporary far point). After moving the fixation unit 40 (liquid crystal panel 41) further from that position to the cloudy position, the main control unit 211 controls the ref measurement projection system 6 and the ref measurement light receiving system 7 to obtain a ring image as the main measurement. get it again. The main control unit 211 causes the eye refractive power calculation unit 221 to calculate the spherical power, the cylindrical power, and the cylindrical axis angle from the analysis result of the ring image obtained in the same manner as described above and the movement amount of the focusing lens 74 . As described above, the eye refractive power calculation unit 221 corresponds to the distance between the inner limiting membrane ILM and the retinal pigment epithelium layer RPE in the macula (macula retinal thickness RT) for the calculated refractive power value. Obtain the measured value of the refractive power value to which the correction value γ is applied.

Further, the eye refractive power calculator 221 obtains the position corresponding to the far point of the subject's eye E (the position corresponding to the far point obtained by the main measurement) from the obtained spherical power and cylindrical power. The main control unit 211 moves the liquid crystal panel 41 to the position corresponding to the far point obtained. In the control unit 210 , the position of the focusing lens 74 and the calculated spherical power are stored in the storage unit 212 . In response to an instruction from the main control unit 211 or a user's operation or instruction to the operation unit 280, the operation of the ophthalmologic apparatus 1000 proceeds to step S3.

When it is determined that the ring image cannot be acquired, the main control unit 211 considers the possibility of the eye being a highly ametropic eye, and moves the ref measurement light source 61 and the focusing lens 74 to the minus power side (for example, -10D), and move it to the plus power side (for example, +10D). The main control unit 211 controls the ref measurement light-receiving system 7 to detect the ring image at each position. If it is still determined that the ring image cannot be acquired, the main control unit 211 executes predetermined measurement error processing. At this time, the operation of the ophthalmologic apparatus 1000 may proceed to step S3. In the control unit 210, information indicating that the result of the ref measurement was not obtained is stored in the storage unit 212. FIG.

(S3: OCT measurement)
First, the main controller 211 moves the fixation unit 40 (liquid crystal panel 41) from the cloudy position to the in-focus position. In some embodiments, the in-focus position is the position of the equivalent spherical power (S+C/2) specified in step S4, or the position of the equivalent spherical power (S+C/2) from which the intensity of the interference signal, etc. becomes maximum. It is a position adjusted to

Subsequently, the main controller 211 turns on the OCT light source 101 and controls the optical scanner 88 to scan a predetermined portion (including the macula) of the fundus oculi Ef with the measurement light LS. For example, detection signals obtained by scanning with the measurement light LS are sent to the image forming section 222 . The image forming unit 222 forms a tomographic image of the fundus oculi Ef from the obtained detection signal.

(S4: Calculate interlayer distance)
Next, the main control section 211 causes the layer region specifying section 232A to specify a predetermined layer region in the fundus based on the scan data acquired in step S3. Similarly, the main control unit 211 causes the edema identification unit 232B to perform edema identification processing in the macular region based on the scan data acquired in step S3. The main control unit 211 causes the layer thickness calculation unit 232C to calculate at least a predetermined interlayer distance such as the macular retinal thickness.

(S5: Calculate retina index)
The main control unit 211 causes the comparison unit 232D to compare the macular retinal thickness calculated in step S4 with the standard data stored in the storage unit 212, and based on the comparison result, the retinal index is generated by the abnormality degree information generation unit 232E. to generate The degree-of-abnormality information generation unit 232E generates a retina index as shown in FIG. 5, for example.

(S6: display)
The main control unit 211 causes the display unit 270 to display the measured refractive power value to which the correction value γ obtained in step S2 is applied and the retinal index calculated in step S5 on the same screen of the display unit 270 .

FIG. 8 shows a display example in step S6 according to the embodiment.

The main control unit 211 causes the display unit 270 to display the anterior segment image IMG1 acquired by the anterior segment observation system 5 in real time. Further, the main control unit 211 superimposes the measured refractive power values of the subject's right eye and left eye, the retinal index, and the tomographic image on the anterior segment image IMG1 for display.

Specifically, the main control unit 211 superimposes the measured value RA of the refractive power of the subject's right eye, the retinal index RID of the right eye, and the tomographic image RIMG of the fundus of the right eye on the anterior segment image IMG1. to display. A retinal index RID is generated based on the interlayer distance of the fundus obtained from the OCT scan performed when the measurement RA was taken. The tomogram RIMG is generated by an OCT scan performed when the measurements RA were acquired. Similarly, the main control unit 211 displays the refractive power measurement value LA of the subject's left eye, the retinal index LID of the left eye, and the tomographic image LIMG of the fundus of the left eye, superimposed on the anterior segment image IMG1. Let A retinal index LID is generated based on the interlayer distance of the fundus obtained from the OCT scan performed when the measurement LA was taken. A tomogram LIMG is generated by an OCT scan performed when the measurements LA were acquired.

By displaying the refractive power measurement value and the retinal index on the display unit 270, when the refractive power value is determined to be abnormal, it is possible to easily determine whether or not the cause lies in the fundus. become.

(S7: Enlarge display?)
Subsequently, the main control unit 211 determines whether or not to enlarge and display the tomographic image displayed in step S6. For example, the main control unit 211 performs a predetermined operation on the operation unit 280 when the examiner who has viewed the measured value, retinal index, or tomographic image displayed in step S6 wants to check the morphology of the fundus in detail. is performed, it is determined whether or not to enlarge the tomographic image.

When it is determined that the tomographic image should be enlarged and displayed (S7: Y), the operation of the ophthalmologic apparatus 1000 proceeds to step S8. When it is determined not to enlarge and display the tomographic image (S7: N), the operation of the ophthalmologic apparatus 1000 ends (END).

(S8: Correct refractive power measurement value)
When it is determined in step S7 that the tomographic image is to be enlarged and displayed (S7: Y), the main control unit 211 causes the measurement value correction unit 233 to correct the refractive power measurement value of the subject's eye E acquired in step S2. Between steps S3 to S8, the intraocular distance calculator 231 calculates the axial length of the eye E to be examined. In step S8, the measured value correction unit 233 corrects the refractive power measured value obtained in step S2 using the correction value γ1 shown in Equation (1).

(S9: display)
The main control unit 211 enlarges and displays the specified tomographic image in step S7, and displays the refractive power measurement value obtained in step S2 and the correction value of the measurement value obtained in step S8. 270 are displayed on the same screen.

FIG. 9 shows a display example in step S9 according to the embodiment.

The main control unit 211 causes the display unit 270 to display a tomographic image LIMG obtained by enlarging the designated tomographic image at a predetermined magnification in step S7. Further, the main control unit 211 causes the display unit 270 to display the refractive power measurement value LA obtained in step S2 and the refractive power measurement value LA1 corrected in step S8 on the same screen.

By displaying the measured value LA and the corrected measured value LA1 together with the tomographic image LIMG on the display unit 270, it is easy to determine whether or not the abnormality in the refractive power value is caused by the morphology of the fundus (in particular, the macula). It becomes possible to judge

With this, the operation of the ophthalmologic apparatus 1000 is completed (end).

As described above, according to the embodiment, by displaying the refractive power measurement value and the retinal index on the display unit 270, when the refractive power value is determined to be abnormal, the cause is the fundus. It becomes possible to easily determine whether or not there is. In addition, by displaying the measured value and the corrected measured value on the display unit 270 together with the tomographic image, it is possible to easily determine whether or not the abnormality in the refractive power value is caused by the morphology of the fundus (particularly, the macular region). judgment becomes possible.

<Modification>
In the above embodiment, the case where the abnormality degree information generating unit 232E generates a retinal index that changes stepwise according to the difference between the acquired refractive power value and the standard data has been described. is not limited to this.

For example, the main control unit according to the modification of the embodiment may change the display color of the retina index in stages according to the difference between the acquired refractive power value and the standard data.

FIG. 10 schematically shows an example of a retinal index number according to a modification of the embodiment.

The main control unit according to the modification causes the display unit 270 to change the display color of the retinal index according to the difference between the acquired refractive power value and the standard data (that is, the degree of abnormality). For example, if the retina index is between 8 and 10, it will be displayed in green; if the retina index is between 4 and 7, it will be displayed in yellow; and if the retina index is between 1 and 3. is displayed in green.

According to this modified example, the display color of the retina index displayed on the display unit 270 is changed according to the degree of abnormality of the retina, so that it is possible to prevent the examiner from overlooking it and to call attention to it. Become.

It is also possible to notify the degree of abnormality of the retina by simple color output, sound output, or the like.

[Action/effect]
Actions and effects of the ophthalmologic apparatus according to the embodiment will be described.

An ophthalmologic apparatus (1000) according to some embodiments includes a refractive power measurement unit (reflection measurement projection system 6, reflection measurement light receiving system 7, and eye refractive power calculation unit 221) and a data collection unit (OCT optical system 8). , a storage unit (212), an analysis unit (232), an abnormality level information generation unit (232E), and a display control unit (control unit 210, main control unit 211). The refractive power measurement unit acquires the measured value of the refractive power of the subject's eye (E). The data collection unit collects data of the fundus (Ef) of the subject's eye using optical coherence tomography. The storage unit stores in advance standard data including a predetermined interlayer distance in the fundus of a normal eye. The analysis unit calculates a predetermined interlayer distance based on the fundus data. The degree-of-abnormality information generation unit generates degree-of-abnormality information representing the degree of abnormality of the fundus based on the predetermined interlayer distance calculated by the analysis unit and the standard data. The display control unit displays the refractive power measurement value and the degree of abnormality information acquired by the refractive power measurement unit on the same screen of the display means (display unit 270).

According to such a configuration, the measured value of the refractive power of the subject's eye obtained by the refractive power measuring unit and the degree of abnormality information representing the degree of abnormality of the fundus based on the standard data and the predetermined interlayer distance in the fundus are displayed. Since the information is displayed on the same screen of the means, when it is determined that the refractive power value is abnormal, it is possible to easily determine whether or not the cause lies in the fundus.

In the ophthalmologic apparatus according to some embodiments, the abnormality degree information generator generates abnormality degree information corresponding to the difference between the standard data and the predetermined interlayer distance calculated by the analysis unit.

According to such a configuration, since the degree of abnormality of the fundus can be represented by simple processing, it is possible to easily determine the degree of abnormality of the fundus when it is determined that the refractive power value is abnormal. Become.

An ophthalmologic apparatus according to some embodiments includes an image forming unit (222) that forms a tomographic image of the fundus based on fundus data, and a display control unit controls the tomographic image formed by the image forming unit, refractive power and the information on the degree of abnormality are displayed on the same screen of the display means.

According to such a configuration, when it is determined that the refractive power value is abnormal, it is possible to easily determine whether or not the cause lies in the fundus while looking at the tomographic image or the like.

In some embodiments of the ophthalmic device, the predetermined interlayer distance is the distance between the retinal pigment epithelium layer and the inner limiting membrane.

According to such a configuration, since it is possible to generate the degree of abnormality information based on the distance between the retinal pigment epithelium layer and the inner limiting membrane, when it is determined that the refractive power value is abnormal, It becomes possible to easily determine whether or not the cause is in the retina.

An ophthalmologic apparatus according to some embodiments includes an edema identification unit (232B) that identifies edema in the fundus based on fundus data, and a refractive power measurement value according to the form of edema identified by the edema identification unit. and a measured value correction unit (233) for correction, and the display control unit causes the display means to display the measured value corrected by the measured value correction unit.

According to such a configuration, edema in the fundus is specified, the measured value of refractive power is corrected according to the specified form of edema, and the corrected measured value is displayed on the display means. When the strength value is determined to be abnormal, it becomes possible to easily determine whether or not the cause is edema.

An ophthalmologic apparatus (1000) according to some embodiments includes a refractive power measurement unit (reflection measurement projection system 6, reflection measurement light receiving system 7, and eye refractive power calculation unit 221) and a data collection unit (OCT optical system 8). , an edema identification unit (232B), a measurement value correction unit (233), and a display control unit (control unit 210, main control unit 211). The refractive power measurement unit acquires the measured value of the refractive power of the subject's eye (E). The data collection unit collects data of the fundus (Ef) of the subject's eye using optical coherence tomography. The edema identifying unit identifies edema in the fundus based on the fundus data. The measurement correction unit corrects the refractive power measurement value according to the form of edema identified by the edema identification unit. The display control section causes the display means (display section 270) to display the measured value corrected by the measured value correction section.

According to such a configuration, edema is identified based on data collected using optical coherence tomography, the measured value of the refractive power of the eye to be examined is corrected according to the identified edema form, and the corrected Since the measured value is displayed on the display means, when it is determined that the refractive power value is abnormal, it is possible to easily determine whether or not the cause is edema.

In the ophthalmologic apparatus according to some embodiments, the measurement value correction unit calculates the axial length of the macula and the distance from the retinal pigment epithelium layer to the inner limiting membrane at the site of edema identified by the edema identification unit and the macular retina. Correct the measurements based on thickness.

According to this configuration, the refractive power measurement value is corrected based on the axial length of the macula, the distance from the retinal pigment epithelium layer to the inner limiting membrane, and the retinal thickness of the macula. It is possible to obtain a refractive power value with high accuracy.

In the ophthalmologic apparatus according to some embodiments, the display control unit causes the refractive power measurement value acquired by the refractive power measurement unit and the measurement value corrected by the measurement value correction unit to be displayed on the same screen of the display means. .

According to such a configuration, since the measured value of the refractive power of the subject's eye and the corrected measured value are displayed on the same screen of the display means, it is possible to easily determine the influence of edema. .

An ophthalmologic information processing program according to some embodiments causes a computer to execute an analysis step, an abnormality degree information generation step, and a display control step. The analysis step calculates a predetermined interlayer distance in the fundus based on the fundus (Ef) data of the subject's eye (E) collected using optical coherence imaging. The degree-of-abnormality information generation step generates degree-of-abnormality information representing the degree of abnormality of the fundus based on the predetermined interlayer distance calculated in the analysis step and standard data including the predetermined interlayer distance in the fundus of the normal eye. The display control step displays the measured value of the refractive power of the subject's eye and the information on the degree of abnormality on the same screen of the display means (display unit 270).

According to such a program, the measured value of the refractive power of the subject's eye and the degree of abnormality information representing the degree of abnormality of the fundus based on the standard data and the predetermined interlayer distance in the fundus are displayed on the same screen of the display means. Therefore, when it is determined that the refractive power value is abnormal, it is possible to easily determine whether or not the cause lies in the fundus.

In the ophthalmologic information processing program according to some embodiments, the abnormality degree information generation step generates abnormality degree information corresponding to the difference between the standard data and the predetermined interlayer distance calculated in the analysis step.

According to such a program, since the degree of abnormality of the fundus can be represented by simple processing, it is possible to easily judge the degree of abnormality of the fundus when the refractive power value is judged to be abnormal. Become.

An ophthalmologic information processing program according to some embodiments includes an image forming step of forming a tomographic image of the fundus based on fundus data, and a display control step includes the tomographic image formed in the image forming step, The measured values and the information on the degree of abnormality are displayed on the same screen of the display means.

According to such a program, when it is determined that the refractive power value is abnormal, it is possible to easily determine whether or not the cause lies in the fundus while viewing a tomographic image or the like.

In the ophthalmic information processing program according to some embodiments, the predetermined interlayer distance is the distance between the retinal pigment epithelium layer and the inner limiting membrane.

According to such a program, since it is possible to generate the degree of abnormality information based on the distance between the retinal pigment epithelium layer and the inner limiting membrane, if the refractive power value is determined to be abnormal, the It becomes possible to easily determine whether or not the cause is in the retina.

An ophthalmologic information processing program according to some embodiments comprises an edema identification step of identifying edema in the fundus based on fundus oculi data, and correcting a refractive power measurement value according to the form of edema identified in the edema identification step. and the display control step causes the display means to display the measured value corrected in the measured value correction step.

According to such a program, edema in the fundus is specified, the refractive power measurement value is corrected according to the specified edema form, and the corrected measurement value is displayed on the display means. When the strength value is determined to be abnormal, it becomes possible to easily determine whether or not the cause is edema.

An ophthalmologic information processing program according to some embodiments causes a computer to execute an edema identification step, a measurement value correction step, and a display control step. The edema identification step identifies edema in the fundus based on the fundus (Ef) data of the subject's eye (E) collected using optical coherence tomography. The measured value correcting step corrects the measured value of the refractive power of the subject's eye according to the form of edema identified in the edema identifying step. The display control step causes the display means (display unit 270) to display the measured value corrected in the measured value correction step.

Such programs identify edema based on data collected using optical coherence tomography, correct the measured refractive power of the subject eye according to the identified form of edema, and correct the Since the measured value is displayed on the display means, when it is determined that the refractive power value is abnormal, it is possible to easily determine whether or not the cause is edema.

In the ophthalmologic information processing program according to some embodiments, the measurement value correcting step includes the axial length of the macula and the distance from the retinal pigment epithelium layer to the inner limiting membrane at the edema site identified in the edema identifying step and the macula Correct the measurements based on partial retinal thickness.

According to such a program, the measured value of refractive power is corrected based on the axial length of the eye in the macula, the distance from the retinal pigment epithelium layer to the inner limiting membrane, and the retinal thickness of the macula. It is possible to obtain a refractive power value with high accuracy.

In the ophthalmologic information processing program according to some embodiments, the display control step causes the measured value of refractive power and the measured value corrected in the measured value correcting step to be displayed on the same screen of the display means.

According to such a program, since the measured value of the refractive power of the eye to be examined and the corrected measured value are displayed on the same screen of the display means, it is possible to easily determine the influence of edema. .

<Others>
The embodiment shown above is merely an example for carrying out the present invention. A person who intends to implement this invention can make arbitrary modifications, omissions, additions, etc. within the scope of the gist of this invention.

In the above embodiment or its modification, the case where the refractive power measurement value is obtained by projecting light onto the subject's eye has been described, but the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this. . An ophthalmic device according to an embodiment may obtain a refractive power measurement value based on wavefront aberration obtained using a known wavefront sensor.

1 Z alignment system 2 XY alignment system 3 Keratometry system 4 Fixation projection system 5 Anterior eye observation system 6 Reflex measurement projection system 7 Reflex measurement light receiving system 8 OCT optical system 9 Processing unit 210 Control unit 211 Main control unit 220 Arithmetic processing Unit 221 Eye refractive power calculation unit 222 Image formation unit 223 Data processing unit 231 Intraocular distance calculation unit 232 Analysis unit 232A Layer area identification unit 232B Edema identification unit 232C Layer thickness calculation unit 232D Comparison unit 232E Abnormality degree information generation unit 233 Measured value Correction unit 1000 Ophthalmic device

Claims (8)

an edema identifying unit that identifies edema in the fundus based on fundus data of a subject eye collected using optical coherence tomography;
Based on the axial length of the macula, the distance from the retinal pigment epithelium layer to the inner limiting membrane at the edema site identified by the edema identification section, and the macular retinal thickness, the measured value of the refractive power of the subject's eye is calculated. a measured value correction unit for correction;
An ophthalmic device, comprising: When AL _ILM is the axial length that is the distance from the corneal vertex to the inner limiting membrane, RT is the macular retinal thickness, MET is the height of edema in the macula, and n is the intraocular equivalent refractive index, the above 2. The ophthalmologic apparatus according to claim 1, wherein the measured value correction unit corrects the measured value by adding a correction value γ1 obtained by the following formula (A) to the measured value.

When AL _ILM is the axial length that is the distance from the corneal vertex to the inner limiting membrane, RT is the macular retinal thickness, MET is the height of edema in the macula, and n is the intraocular equivalent refractive index, the above The ophthalmology according to claim 1, wherein the measured value correction unit corrects the measured value by adding a correction value γ1 obtained by the following formulas (B) and (C) to the measured value. Device.

The ophthalmologic apparatus according to any one of claims 1 to 3, further comprising a display control unit that causes a display unit to display the measured value corrected by the measured value correction unit. an edema identifying step of identifying edema in the fundus based on fundus data of the eye to be examined collected using optical coherence tomography;
Based on the eye axial length in the macula, the distance from the retinal pigment epithelium layer to the inner limiting membrane at the edema site identified in the edema identification step, and the macular retinal thickness, the measured value of the refractive power of the eye to be examined is calculated. a measured value correction step to correct;
ophthalmic information processing program that causes a computer to execute When AL _ILM is the axial length that is the distance from the corneal vertex to the inner limiting membrane, RT is the macular retinal thickness, MET is the height of edema in the macula, and n is the intraocular equivalent refractive index, the above 6. The ophthalmologic information processing program according to claim 5, wherein the measured value correcting step corrects the measured value by adding a correction value γ1 obtained by the following formula (D) to the measured value.

When AL _ILM is the axial length that is the distance from the corneal vertex to the inner limiting membrane, RT is the macular retinal thickness, MET is the height of edema in the macula, and n is the intraocular equivalent refractive index, the above 6. The ophthalmology according to claim 5, wherein the measured value correction step corrects the measured value by adding a correction value γ1 obtained by the following formulas (E) and (F) to the measured value. Information processing program.

8. The ophthalmologic information processing program according to any one of claims 5 to 7, further comprising a display control step of causing a display unit to display the measured value corrected in the measured value correcting step.

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