JP7057186B2 - Ophthalmology equipment and ophthalmology information processing program - Google Patents

Description

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

In recent years, the number of people with unaided eyesight, which is considered to be myopia, has continued to increase, which has become a major social problem. The causes of myopia are thought to include genetic and environmental factors. Since myopia not only causes deterioration of quality of life (QOL) but also can be a risk factor for blindness, measures against the progression of myopia are one of the important issues.

One of the measures against the progression of myopia is the prediction of the progression of myopia. Predicting the progression of myopia enables early implementation of measures such as alerting, proposing myopia suppression, and recommending regular medical examinations for myopia due to genetic factors. In addition, predicting the progress of myopia enables early implementation of measures such as reviewing lifestyle habits for myopia due to environmental factors, for example.

For example, Patent Document 1 discloses a myopia progression diagnostic device for diagnosing myopia progression. This myopia progression diagnostic device irradiates light in a direction forming a predetermined angle with respect to the eye axis to acquire optical data of the peripheral visual field of the fundus, and analyzes the acquired optical data to focus on the measured light. The presence or absence of myopia progression is predicted from the anterior-posterior refractive index.

Japanese Patent No. 5676730

However, in recent studies on the progression of myopia, it is becoming common that no correlation is found between myopia and the morphology of the peripheral visual field of the fundus. In particular, predicting the progression of axial myopia based on optical data of the peripheral visual field of the fundus may rather reduce reliability.

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 predicting the progression of axial myopia with higher reliability.

The first aspect of some embodiments is an intraocular distance measuring unit that acquires a measured value of the refractive force of the eye to be inspected, and an intraocular distance measuring unit that acquires a measured value of one or more intraocular distances in the eye to be inspected. , Acquired by the refractive force measuring unit and a storage unit that previously stores standard data in which the information of the measured person is associated with the refractive force of the eye of the subject to be measured who is a normal eye and the intraocular distance of 1 or more. Based on the measured value of the refractive force, the measured value of the intraocular distance of 1 or more acquired by the intraocular distance measuring unit, the information of the subject, and the standard data, the eye to be inspected is the axis. It is an ophthalmic apparatus including an analysis unit for determining whether or not the patient has sexual myopia.

In the second aspect of some embodiments, in the first aspect, the analysis unit comprises the measured value of the refractive power, the measured value of the intraocular distance of one or more, the information of the subject, and the standard data. By comparing with and, it is determined whether or not the eye to be inspected has axial myopia.

A third aspect of some embodiments is a means of displaying information corresponding to a determination result indicating whether or not the eye to be inspected is axial myopia obtained by the analysis unit in the first aspect or the second aspect. Includes a control unit to be displayed on.

In the fourth aspect of some embodiments, in any one of the first to third aspects, the analysis unit is based on the standard data the refractive power of the eye, the distance within one or more of the eye, and the said. By referring to the first analysis information obtained in advance with at least one of the information of the person to be measured as a variable, the progress information of the axial myopia is generated.

A fifth aspect of some embodiments is a refractive force measuring unit that acquires a measured value of the refractive force of the eye to be inspected, and an intraocular distance measuring unit that acquires a measured value of one or more intraocular distances in the eye to be inspected. , Acquired by the refractive force measuring unit and a storage unit that previously stores standard data in which the information of the measured person is associated with the refractive force of the eye of the subject to be measured who is a normal eye and the intraocular distance of 1 or more. The axis of the eye to be inspected based on the measured value of the refractive force, the measured value of the intraocular distance of 1 or more acquired by the intraocular distance measuring unit, the information of the subject, and the standard data. It is an ophthalmic apparatus including an analysis unit that generates progress information of sexual myopia.

In the sixth aspect of some embodiments, in any one of the first to fifth aspects, the analysis unit measures two or more of the refractive forces acquired by the refractive force measuring unit at different measurement timings. The subject is based on the values, the two or more measurement values of the one or more intraocular distances acquired by the intraocular distance measuring unit at different measurement timings, the information of the subject, and the standard data. Generates information on the progress of axial myopia in optometry.

A seventh aspect of some embodiments is a refractive force measuring unit that acquires a measured value of the refractive force of the eye to be inspected, and an intraocular distance measuring unit that acquires a measured value of one or more intraocular distances in the eye to be inspected. , A storage unit that stores in advance standard data in which information on the subject is associated with the refractive force of the subject's eye, which is a normal eye, and the intraocular distance of one or more, and the refractive force at different measurement timings. Two or more measured values of the refractive force acquired by the measuring unit, two or more measured values of the one or more intraocular distance acquired by the intraocular distance measuring unit at different measurement timings, and the subject. It is an ophthalmologic apparatus including an analysis unit that generates progress information of axial myopia of the subject eye based on the information of the above and the standard data.

In the eighth aspect of some embodiments, in the sixth or seventh aspect, the analysis unit determines the refractive power of the eye and the change in the refractive power of the eye based on the standard data, and the above-mentioned intraocular distance of one or more. And the change in the intraocular distance of one or more, and the second analysis information obtained in advance with at least one of the information of the person to be measured as a variable, the progress information of the axial myopia is generated.

In the ninth aspect of some embodiments, in any of the fourth to eighth aspects, the progress information is the refractive power after the measurement timing of at least one of the refractive power and the intraocular distance of one or more. And at least one estimate of the intraocular distance of one or more.

A tenth aspect of some embodiments includes, in any one of the fourth to ninth aspects, a control unit that causes the display means to display the progress information obtained by the analysis unit.

In the eleventh aspect of some embodiments, in any one of the first to tenth aspects, the information of the subject and the information of the subject include age and gender.

In the twelfth aspect of some embodiments, in any one of the first to eleventh aspects, the subject's information includes eye characteristic information of a close relative of the subject.

In the thirteenth aspect of some embodiments, in any one of the first to twelfth aspects, the one or more intraocular distance includes an axial length and a choroidal thickness.

In the 14th aspect of some embodiments, in the 13th aspect, the choroid is the choroid in the fovea, the average choroid in the vicinity of the fovea, and each of a plurality of quadrants obtained by dividing the vicinity of the fovea. It includes at least one of the average choroidal thickness and the choroidal thickness around the macula.

In the fifteenth aspect of some embodiments, in any one of the first to the fourteenth aspects, the intraocular distance measuring unit divides the light from the light source into a reference light and a measurement light, and divides the measurement light into a reference light and a measurement light. Based on the OCT optical system that projects onto the eye to be inspected and detects the interference light between the return light of the measurement light from the eye to be inspected and the reference light, and the detection result of the interference light obtained by the OCT optical system. The intraocular distance calculation unit for obtaining the intraocular distance of 1 or more is included.

A sixteenth aspect of some embodiments is an acquisition step of acquiring a measured value of the refractive force of the eye to be inspected, a measured value of one or more intraocular distances in the eye to be inspected, and information on the subject, and the acquisition step. The measured value of the refractive force, the measured value of the intraocular distance of 1 or more, and the information of the subject, the refractive force of the eye of the subject who is a normal eye, and the intraocular distance of 1 or more. It is an ophthalmic information processing program for causing a computer to execute an analysis step of determining whether or not the eye to be inspected has axial myopia based on standard data in which the information of the subject to be measured is associated with the distance. ..

In the 17th aspect of some embodiments, in the 16th aspect, the analysis step comprises the measurement value of the refractive power, the measurement value of the intraocular distance of 1 or more, the information of the subject, and the standard data. By comparing the above, it is determined whether or not the eye to be inspected has axial myopia.

In the eighteenth aspect of some embodiments, the means for displaying information corresponding to the determination result indicating whether or not the eye to be inspected is axial myopia obtained in the analysis step in the sixteenth aspect or the seventeenth aspect. Includes control steps to display on.

A nineteenth aspect of some embodiments is an acquisition step of acquiring the measured value of the refractive force of the eye to be inspected, the measured value of one or more intraocular distances in the eye to be inspected, and the information of the subject, and the acquisition step. The measured value of the refractive force acquired in the above, the measured value of the intraocular distance of 1 or more, the information of the subject, the refractive force of the eye of the subject who is a normal eye, and the eye of 1 or more. It is an ophthalmic information processing program for causing a computer to execute an analysis step of generating progress information of axial myopia of the eye to be inspected based on standard data in which the information of the subject is associated with an internal distance.

In the twentieth aspect of some embodiments, in any of the sixteenth to nineteenth aspects, the analysis step is a measurement of two or more of the refractive powers acquired in the acquisition step at different measurement timings. Based on two or more measured values of the above-mentioned one or more intraocular distances, the information of the subject, and the standard data, the progress information of the axial myopia of the subject is generated.

The 21st aspect of some embodiments is different from each other, such as a measurement value of the refractive force of the eye to be inspected, a measurement value of one or more intraocular distances in the eye to be inspected, and an acquisition step for acquiring information on the subject. Two or more measurement values of the refractive force acquired in the acquisition step at the timing, two or more measurement values of the intraocular distance of one or more, information of the subject, and the subject having a normal eye. An analysis step of generating progressive myopia progression information for the eye to be inspected is performed on a computer based on standard data in which the information of the subject is associated with the refractive force of the eye and the intraocular distance of one or more. It is an ophthalmic information processing program to make it.

In the 22nd aspect of some embodiments, in any of the 19th to 21st aspects, the progress information is the refractive power after the measurement timing of at least one of the refractive power and the intraocular distance of one or more. And at least one estimate of the intraocular distance of one or more.

The 23rd aspect of some embodiments includes, in any of the 19th to 22nd aspects, a control step for causing the display means to display the progress information obtained in the analysis step.

In the 24th aspect of some embodiments, in any of the 16th to 23rd aspects, the information of the subject and the information of the subject include age and gender.

In the 25th aspect of some embodiments, in any of the 16th to 24th aspects, the subject's information includes eye characteristic information of the subject's close relatives.

In the 26th aspect of some embodiments, in any of the 16th to 25th aspects, the one or more intraocular distance includes an axial length and a choroidal thickness.

In the 27th aspect of some embodiments, in the 26th aspect, the choroid is the choroid in the fovea, the average choroid in the vicinity of the fovea, and each of a plurality of quadrants obtained by dividing the vicinity of the fovea. It includes at least one of the average choroidal thickness and the choroidal thickness around the macula.

INDUSTRIAL APPLICABILITY According to the present invention, it becomes possible to provide a new technique for predicting the progression of axial myopia with higher reliability.

It is a schematic diagram which shows the structural example of the optical system of the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram which shows the structural example of the optical system of the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the processing system of the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the processing system of the ophthalmic apparatus which concerns on embodiment. It is a schematic diagram which shows the flow of the operation example of the ophthalmologic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the operation of the ophthalmologic apparatus which concerns on embodiment. It is a schematic diagram which shows the flow of the operation example of the ophthalmologic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the operation of the ophthalmologic apparatus which concerns on embodiment. It is a schematic diagram for demonstrating the operation of the ophthalmologic apparatus which concerns on embodiment.

An example of an ophthalmic apparatus and an embodiment of an ophthalmic information processing program according to the present invention will be described in detail with reference to the drawings. In addition, the description contents of the document cited in this specification and arbitrary known techniques can be incorporated into the following embodiments.

The ophthalmic apparatus according to the embodiment has a function of an ophthalmic information processing apparatus. The function of the ophthalmic information processing apparatus is realized by a computer that executes processing according to the ophthalmic information processing program. The ophthalmic information processing apparatus includes a processor and a storage unit in which the ophthalmic information processing program is stored in advance, and the processor executes processing according to the ophthalmic information processing program read from the storage unit to obtain the ophthalmic information processing apparatus. Realize the function.

The ophthalmic apparatus according to the embodiment can perform measurement of refractive power (ref measurement) and measurement and imaging using optical coherence tomography (hereinafter referred to as OCT).

Hereinafter, in the embodiment, the case where the swept source type OCT method is used in the measurement using OCT will be described in particular, but for an ophthalmic apparatus using another type (for example, spectral domain type) OCT, It is also possible to apply the configuration according to the embodiment.

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

The subjective test is a measurement method for acquiring information by using the response from the subject. The subjective test includes a subjective refraction measurement such as a distance test, a near test, a contrast test, and a glare test, and a visual field test.

Objective measurement is a measurement method for acquiring information about an eye to be inspected mainly by using a physical method without referring to a response from the subject. Objective measurement includes measurement for acquiring the characteristics of the eye to be inspected and photographing for acquiring an image of the eye to be inspected. Other objective measurements include kerato measurement, intraocular pressure measurement, fundus photography and the like.

Hereinafter, the fundus conjugate position is a position optically coupled to the fundus of the eye to be inspected in a state where the alignment is completed, and means a position optically coupled to the fundus of the eye to be inspected or its vicinity thereof. Similarly, the pupil-coupled position is a position that is optically coupled to the pupil of the eye to be inspected in the state where the alignment is completed, and means a position that is optically coupled to or in the vicinity of the pupil of the eye to be inspected. ..

In the ophthalmic apparatus according to the embodiment, the eye to be inspected is the axis based on the measured value obtained by the refractive power measurement, the intraocular distance of 1 or more obtained from the measurement result of the OCT measurement, and the information of the subject. Determine if you have sexual myopia. The ophthalmic apparatus according to some embodiments determines whether or not the eye to be inspected has axial myopia by comparing with standard data. The standard data is statistically derived data based on a large number of measurement data of normal eyes. The ophthalmologic apparatus according to some embodiments is based on the measured values obtained by the refractive power measurement, one or more intraocular distances obtained from the measurement results of the OCT measurement, and the information of the subject. Generates progress information on sexual myopia.

In some embodiments, one or more intraocular distances include axial length and choroidal thickness. The choroid thickness is at least one of the choroid thickness in the fovea, the average choroid near the fovea, the average choroid in each of the plurality of quadrants obtained by dividing the vicinity of the fovea, and the choroid around the macula. include.

In some embodiments, the subject's information and the subject's information include age and gender. In some embodiments, the subject's information includes eye characteristic information of the subject's close relatives. Relatives are relatives within the second degree of kinship of the subject. Relatives are preferably the subject's father or mother. The eye characteristic information includes the refractive power value.

The progress information includes information showing the progress of axial myopia at the time of measurement and information showing the progress of future axial myopia after the time of measurement. In some embodiments, the information representing the degree of progression of future axial myopia includes predicted values of predetermined intraocular parameters such as refractive power values and axial lengths.

<Composition of optical system>
FIG. 1 shows a configuration example of an optical system of an ophthalmic apparatus according to an embodiment. The ophthalmic apparatus 1000 according to the embodiment includes an optical system for observing the eye E to be inspected, an optical system for inspecting the eye E to be inspected, and a dichroic mirror for wavelength-separating the optical paths of these optical systems. An anterior eye portion observation system 5 is provided as an optical system for observing the eye E to be inspected. An OCT optical system and a ref measurement optical system (refractive power measurement optical system) are provided as an optical system for inspecting the eye E to be inspected.

The ophthalmic apparatus 1000 includes a Z alignment system 1, an XY alignment system 2, a kerato measurement system 3, a fixative projection system 4, an anterior ocular segment observation system 5, a reflex measurement projection system 6, a reflex measurement light receiving system 7, and an OCT optical system 8. including. In the following, for example, the anterior eye observation system 5 uses light of 940 nm to 1000 nm, and the reflex measurement optical system (ref measurement projection system 6, reflex measurement light receiving system 7) uses light of 830 nm to 880 nm, and the fixation projection system is used. It is assumed that 4 uses light of 400 nm to 700 nm, and OCT optical system 8 uses light of 1000 nm to 1100 nm.

(Anterior eye observation system 5)
The anterior eye portion observation system 5 captures a moving image of the anterior segment of the eye to be inspected E. In the optical system via the anterior eye portion observation system 5, the image pickup surface of the image pickup element 59 is arranged at the pupil conjugate position. The anterior eye portion illumination light source 50 irradiates the anterior segment of the eye E to be inspected with illumination light (for example, infrared light). The light reflected by the anterior segment of the eye E to be inspected passes through the objective lens 51, passes through the dichroic mirror 52, passes through the hole formed in the diaphragm (teressen diaphragm) 53, and passes through the half mirror 23. , Passes through the relay lenses 55 and 56, and passes through 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 ocular segment observation system 5. In the dichroic mirror 52, the optical path synthesis surface that synthesizes these optical paths is arranged so as to be inclined with respect to the optical axis of the objective lens 51. The light transmitted through the dichroic mirror 76 is imaged on the image pickup surface of the image pickup element 59 (area sensor) by the image pickup lens 58. The image pickup device 59 performs image pickup and signal output at a predetermined rate. The output (video signal) of the image pickup device 59 is input to the processing unit 9 described later. The processing unit 9 displays the front eye portion image E'based on this video signal on the display screen 10a of the display unit 10 described later. The anterior eye portion image E'is, for example, an infrared moving image.

(Z alignment system 1)
The Z alignment system 1 projects light (infrared light) for alignment in the optical axis direction (front-back direction, Z direction) of the anterior eye portion observation system 5 onto the eye E to be inspected. The light output from the Z alignment light source 11 is projected onto the corneal Cr of the eye E to be inspected, 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 apex of the cornea changes in the optical axis direction of the anterior eye portion observation system 5, the projection position of light on the sensor surface of the line sensor 13 changes. The processing unit 9 obtains the position of the corneal apex of the eye E to be inspected based on the projection position of light on the sensor surface of the line sensor 13, and controls the mechanism for moving the optical system based on this to execute Z alignment.

(XY alignment system 2)
The XY alignment system 2 emits light (infrared light) for alignment in a direction orthogonal to the optical axis of the anterior segment observation system 5 (horizontal direction (X direction), vertical direction (Y direction)). Irradiate to. 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. The 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 eye E to be inspected through the anterior eye observation system 5. The reflected light from the corneal Cr of the eye E to be inspected is guided to the image pickup device 59 through the anterior ocular segment observation system 5.

The image (bright spot image) Br based on this reflected light is included in the anterior eye portion image E'. The processing unit 9 displays the front eye portion image E'including the bright spot image Br and the alignment mark AL on the display screen of the display unit. When manually performing XY alignment, the user operates the optical system so as to guide the bright spot image Br in the alignment mark AL. When the alignment is automatically performed, the processing unit 9 controls a 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 kerato measurement system 3 projects a ring-shaped luminous flux (infrared light) for measuring the shape of the corneal Cr of the eye E to be inspected onto the corneal Cr. The kerato plate 31 is arranged between the objective lens 51 and the eye E to be inspected. A keratling light source 32 is provided on the back surface side (objective lens 51 side) of the kerato plate 31. By illuminating the kerato plate 31 with the light from the keratling light source 32, a ring-shaped luminous flux (arc-shaped or circumferential-shaped measurement pattern) is projected onto the corneal Cr of the eye E to be inspected. The reflected light (keratling image) from the corneal Cr of the eye E to be inspected is detected by the image pickup device 59 together with the anterior eye portion image E'. The processing unit 9 calculates a corneal shape parameter representing the shape of the corneal Cr by performing a known calculation based on this keratling image.

(Ref measurement projection system 6, reflex measurement light receiving system 7)
The reflex measurement optical system includes a reflex measurement projection system 6 and a reflex measurement light receiving system 7 used for refractive power measurement. The reflex measurement projection system 6 projects a luminous flux for measuring refractive power (for example, a ring-shaped luminous flux) (infrared light) onto the fundus Ef. The reflex measurement light receiving system 7 receives the return light of this luminous flux from the eye E to be inspected. The reflex measurement projection system 6 is provided in an optical path branched by a perforated prism 65 provided in the optical path of the reflex measurement light receiving system 7. The hole portion formed in the hole opening prism 65 is arranged at the pupil conjugate position. In the optical system via the reflex measurement light receiving system 7, the image pickup surface of the image pickup element 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-intensity light source. The reflex measurement light source 61 is movable in the optical axis direction. The reflex measurement light source 61 is arranged at the fundus conjugate position. The light output from the reflex measurement light source 61 passes through the relay lens 62 and is incident on the conical surface of the conical prism 63. The light incident on the conical surface is deflected and emitted from the bottom surface of the conical prism 63. The light emitted from the bottom surface of the conical prism 63 passes through the translucent portion formed in a ring shape on the ring diaphragm 64. The light (ring-shaped luminous flux) that has passed through the translucent portion of the ring diaphragm 64 is reflected by the reflecting surface formed around the hole portion of the perforated prism 65, passes through the rotary prism 66, and is reflected by the dichroic mirror 67. Ru. 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 inspected. The rotary prism 66 is used for averaging the light amount distribution of the ring-shaped luminous flux with respect to the blood vessel or the diseased part of the fundus Ef and reducing the speckle noise caused by the light source.

The return light of the ring-shaped luminous flux projected on the fundus Ef passes through the objective lens 51 and is reflected by the dichroic mirror 52 and the dichroic mirror 67. The return light reflected by the dichroic mirror 67 passes through the rotary prism 66, passes through the hole portion of the perforated prism 65, passes through the relay lens 71, is reflected by the reflection mirror 72, and is reflected by the relay lens 73 and the focusing lens. Pass through 74. The focusing lens 74 can move along the optical axis of the reflex measurement light receiving system 7. The light that has passed through the focusing lens 74 is reflected by the reflection mirror 75, reflected by the dichroic mirror 76, and imaged on the image pickup surface of the image pickup element 59 by the image pickup lens 58. The processing unit 9 calculates the refractive power value of the eye E to be inspected by performing a known calculation based on the output from the image sensor 59. For example, the refractive power value includes spherical power, astigmatic power and astigmatic axis angle, or equivalent spherical power.

(Fixation projection system 4)
The OCT optical system 8, which will be described later, is provided in an optical path whose wavelength is separated from the optical path of the reflex measurement optical system by the dichroic mirror 67. The fixative projection system 4 is provided in the optical path branched from the optical path of the OCT optical system 8 by the dichroic mirror 83.

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

The liquid crystal panel 41, which is controlled by the processing unit 9, displays a pattern representing a fixative. By changing the display position of the pattern on the screen of the liquid crystal panel 41, the fixative position of the eye E to be inspected can be changed. The fixative position of the eye E to be inspected includes a position for acquiring an image centered on the macula of the fundus Ef, a position for acquiring an image centered on the optic disc, and a position between the macula and the optic disc. There is a position for acquiring an image centered on the center of the fundus between the two. It is possible to arbitrarily change the display position of the pattern representing the fixative.

The light from the liquid crystal panel 41 passes through the relay lens 42, passes through the dichroic mirror 83, passes through the relay lens 82, is reflected by the reflection mirror 81, passes through the dichroic mirror 67, and is reflected by the dichroic mirror 52. .. The light reflected by the dichroic mirror 52 passes through the objective lens 51 and is projected onto the fundus Ef. In some embodiments, each of the liquid crystal panel 41 and the relay lens 42 can move independently 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 face of the optical fiber f1 is coupled to the imaging site (fundus Ef or anterior ocular segment) and the optical system based on the result of the reflex measurement performed before the OCT measurement. ..

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

The 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 sweep type (wavelength scanning type) light source capable of sweeping (scanning) the wavelength of emitted light, similar to a general swept source type OCT device. Consists of including. The wavelength sweep type light source is configured to include a laser light source including a resonator. The OCT light source 101 changes the output wavelength with time in a near-infrared wavelength band that cannot be visually recognized by the human eye.

As illustrated in FIG. 2, the OCT unit 100 is provided with an optical system for performing a swept source OCT. This optical system includes an interference optical system. This interference optical system has a function of dividing the light from the wavelength variable light source (wavelength sweep type light source) into the measurement light and the reference light, and the return light of the measurement light from the eye E to be inspected and the reference light via the reference light path. It has a function of generating interference light by superimposing the light sources and a function of detecting the interference light. The detection result (detection signal) of the interference light obtained by the interference optical system is a signal showing 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 wavelength 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 divided into the measurement light LS and the reference light LR.

The reference light LR is guided to the collimator 111 by the optical fiber 110, converted into a parallel light flux, passes through the optical path length correction member 112 and the dispersion compensation member 113, and is guided to the corner cube 114. The optical path length correction member 112 acts to match the optical path length of the reference light LR with the optical path length of the measured light LS. The dispersion compensating 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 is converted from a parallel luminous flux to a focused luminous flux by a collimator 116 via a dispersion compensating member 113 and an optical path length correction member 112, and is incident on the optical fiber 117. The reference light LR incident on the optical fiber 117 is guided by the polarization controller 118 to adjust its polarization state, is guided to the attenuator 120 by the optical fiber 119 to adjust the amount of light, and is 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 and converted into a parallel light beam by the collimator lens unit 89, and passes through the optical scanner 88, the focusing lens 87, the relay lens 85, and the reflection mirror 84. However, it is reflected by the dichroic mirror 83.

The optical scanner 88 deflects the measurement light LS one-dimensionally or two-dimensionally. The optical scanner 88 includes, for example, a first galvano mirror and a second galvano mirror. The first galvano mirror deflects the measurement light LS so as to scan the imaging site (fundibular Ef or anterior eye portion) in the horizontal direction orthogonal to the optical axis of the OCT optical system 8. The second galvano mirror deflects the measurement light LS deflected by the first galvano mirror so as to scan the imaging region in the direction perpendicular to the optical axis of the OCT optical system 8. Examples of the scanning mode of the measured optical LS by the optical scanner 88 include horizontal scan, vertical scan, cross scan, radial scan, circular scan, concentric circular scan, and spiral scan.

The measurement light LS reflected by the dichroic mirror 83 passes through the relay lens 82, is reflected by the reflection mirror 81, is transmitted through the dichroic mirror 67, is reflected by the dichroic mirror 52, is reflected by the objective lens 51, and is reflected by the objective lens 51. Incident to. The measurement light LS is scattered and reflected at various depth positions of the eye E to be inspected. The return light of the measurement light LS from the eye E to be inspected travels in the same direction as the outward path in the opposite direction, is guided to the fiber coupler 105, and reaches the fiber coupler 122 via the optical fiber 128.

The fiber coupler 122 combines (interferes with) the measurement light LS incident via the optical fiber 128 and the reference light LR incident via the optical fiber 121 to generate interference light. The fiber coupler 122 generates a pair of interference light LCs by branching the interference light at a predetermined branching ratio (for example, 1: 1). The pair of interference light LCs are guided to the detector 125 through the optical fibers 123 and 124, respectively.

The detector 125 is, for example, a balanced photodiode. The balanced photodiode includes a pair of photodetectors that detect each pair of interference light LCs, and outputs the difference between the pair of detection results obtained by these photodetectors. The detector 125 sends this output (detection signal) to the DAT (Data Acquisition System) 130.

A clock KC is supplied to the DAQ 130 from the OCT light source 101. 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 tunable light source. The OCT light source 101 optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then sets 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 unit 220 of the processing unit 9. The arithmetic processing unit 220 forms a reflection intensity profile in each A line by, for example, performing a Fourier transform or the like on the spectral distribution based on the sampling data for each series of wavelength scans (for each A line). Further, the arithmetic processing unit 220 forms image data by imaging the reflection intensity profile of each A line.

In this example, the corner cube 114 for changing the length of the optical path (reference optical path, reference arm) of the reference optical path LR is provided, but the measured optical path length and the reference optical path length are provided by using an optical member other than these. It is also possible to change the difference with.

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

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

The processing unit 9 controls each unit of the ophthalmic apparatus 1000. Further, the processing unit 9 can execute various arithmetic processes. The processing unit 9 includes a processor. The functions of the processor are, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, a SPLD (Simple Program)). , FPGA (Field Programmable Gate Array)) and the like. The processing unit 9 realizes the function according to the embodiment by reading and executing, for example, a program stored in a storage circuit or a storage device.

The processing unit 9 is an example of the "ophthalmology 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 "ophthalmology information processing program" according to the embodiment.

The processing unit 9 includes a control unit 210 and an arithmetic processing unit 220. Further, the ophthalmic apparatus 1000 includes a moving mechanism 200, a display unit 270, an operation unit 280, and a communication unit 290.

The moving mechanism 200 includes a Z alignment system 1, an XY alignment system 2, a kerato measurement system 3, a fixative projection system 4, an anterior eye observation system 5, a reflex measurement projection system 6, a reflex measurement light receiving system 7, an OCT optical system 8, and the like. It is a mechanism for moving the head portion in which the optical system of the above is housed in the front-back and left-right directions. For example, the moving mechanism 200 is provided with an actuator that generates a driving force for moving the head portion and a transmission mechanism that transmits the driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is composed of, for example, a combination of gears or a rack and pinion. The control unit 210 (main control unit 211) controls the moving mechanism 200 by sending a control signal to the actuator.

(Control unit 210)
The control unit 210 includes a processor and controls each unit of the ophthalmologic device. The control unit 210 includes a main control unit 211 and a storage unit 212. A computer program for controlling the ophthalmologic device is stored in the storage unit 212 in advance. The computer program includes 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. When the main control unit 211 operates according to such a computer program, the control unit 210 executes the control process.

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

The control for the XY alignment system 2 includes the control of the XY alignment light source 21 and the like. The control of the XY alignment light source 21 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. As a result, the XY alignment light source 21 is switched between lighting and non-lighting, and the amount of light is changed. The main control unit 211 captures the signal detected by the image pickup device 59, and determines the position of the bright spot image based on the return light of the light from the XY alignment light source 21 based on the captured signal. The main control unit 211 controls the movement mechanism 200 so that the displacement from the position of the bright spot image Br with respect to a predetermined target position (for example, the center position of the alignment mark AL) is canceled, and moves the head unit in the left-right / up-down direction. Move (XY alignment).

The control for the kerato measurement system 3 includes the control of the keratling light source 32 and the like. The control of the keratling light source 32 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. As a result, the lighting and non-lighting of the keratling light source 32 are switched, and the amount of light is changed. The main control unit 211 causes the arithmetic processing unit 220 to perform a known calculation on the keratling image detected by the image sensor 59. As a result, the corneal shape parameter of the eye E to be inspected is obtained.

Controls for the fixative projection system 4 include control of the liquid crystal panel 41 and movement control of the fixative unit 40. The control of the liquid crystal panel 41 includes turning on / off the display of the fixative and switching the display position of the fixative.

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

The control for the anterior eye portion observation system 5 includes the control of the anterior eye portion illumination light source 50, the control of the image pickup element 59, and the like. The control of the anterior eye illumination light source 50 includes turning on and off the light source, adjusting the amount of light, adjusting the aperture, and the like. As a result, the lighting of the frontal eye illumination light source 50 can be switched between lighting and non-lighting, and the amount of light can be changed. The control of the image pickup element 59 includes exposure adjustment, gain adjustment, detection rate adjustment, and the like of the image pickup element 59. The main control unit 211 captures the signal detected by the image pickup device 59, and causes the arithmetic processing unit 220 to perform processing such as forming an image based on the captured signal.

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

The control for the reflex measurement light receiving system 7 includes the control of the focusing lens 74 and the like. Control of the focusing lens 74 includes control of movement of the focusing lens 74 in the optical axis direction. For example, the reflex measurement light receiving system 7 includes a moving mechanism for moving the focusing lens 74 in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, and moves the focusing lens 74 in the optical axis direction. The main control unit 211 illuminates the reflex measurement light source 61 and the focusing lens 74, for example, according to the refractive power of the eye E to be inspected so that the reflex measurement light source 61, the fundus Ef, and the image pickup element 59 are optically coupled. It can be moved in the axial direction.

The control for the OCT optical system 8 includes the control of the OCT light source 101, the control of the optical scanner 88, the control of the focusing lens 87, the control of the corner cube 114, the control of the detector 125, the 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. The control of the optical scanner 88 includes control of the scanning position, scanning range and scanning speed by the first galvano mirror, control of the scanning position, scanning range and scanning speed by the second galvano mirror and the like.

To control the in-focus lens 87, control the movement of the in-focus lens 87 in the optical axis direction, control the movement of the in-focus lens 87 to the in-focus reference position corresponding to the imaging region, and the movement range corresponding to the imaging region (focus). There is 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, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the moving mechanism by sending a control signal to the actuator, and moves the focusing lens 87 in the optical axis direction. In some embodiments, the ophthalmic apparatus is provided with a holding member that holds the focusing lenses 74 and 87 and a drive unit that drives the holding member. The main control unit 211 controls the movement of the focusing lenses 74 and 87 by controlling the drive unit. For example, the main control unit 211 may move the focusing lens 87 in conjunction with the movement of the focusing lens 74, and then move only the focusing lens 87 based on the intensity of the interference signal.

The control of the corner cube 114 includes movement control along the optical path of the corner cube 114. For example, the OCT optical system 8 includes a moving mechanism that moves the corner cube 114 in a direction along an optical path. Similar to the moving mechanism 200, the moving mechanism is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 211 controls the movement mechanism by sending a control signal to the actuator, and moves the corner cube 114 in the direction along the optical path. The control of the detector 125 includes exposure adjustment, gain adjustment, detection rate adjustment, and the like 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 image formation based on the sampled signal.

Further, the main control unit 211 causes the display unit 270 to display information corresponding to the processing result of the data processing unit 223, which will be described later, as the display control unit. The processing results of the data processing unit 223 include the intraocular distance calculated by the intraocular distance calculation unit 231, the determination result by the determination unit 232, and the progress information of axial myopia obtained by the myopia progression estimation unit 233.

Further, the main control unit 211 performs a process of writing data to the storage unit 212 and a process of reading data from the storage unit 212.

(Memory 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 measurement results, tomographic image data, fundus image image data, eye test subject information, subject information, standard data, and the like. be. The eye test information includes information related to the test eye such as left eye / right eye identification information. The subject information includes information about the subject such as patient ID, name, age, gender, height, and weight of the subject. In some embodiments, the subject information is information obtained from an electronic medical record. In some embodiments, the eye-tested information and the subject-examined information are information input by the examiner or the subject using the operation unit 280. The standard data is statistically derived from a large number of measurement data of normal eyes and the information of the subject of the measurement data, and is called normal eye data (normalative data) or the like. In some embodiments, the standard data is a group of data in which a large number of measurement data of a normal eye are associated with the information of the subject of the measurement data. The subject's information includes the age and gender of the subject. The subject's information for some embodiments includes, for example, age, gender, height, weight. In some embodiments, the subject information includes information on items similar to the subject information. Further, various programs and data for operating the ophthalmic apparatus are stored in the storage unit 212.

(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 Calculation Unit 221)
The eye refractive power calculation unit 221 receives a ring image (pattern image) obtained by receiving the return light of the ring-shaped luminous flux (ring-shaped measurement pattern) projected on the fundus Ef by the reflex measurement projection system 6 by the image pickup element 59. ) Is analyzed. For example, the optical power calculation unit 221 obtains the position of the center of gravity of the ring image from the brightness distribution in the image in which the obtained ring image is drawn, and obtains the brightness distribution along a plurality of scanning directions radially extending from the position of the center of gravity. , The ring image is specified from this brightness distribution. Subsequently, the optical power calculation unit 221 obtains an approximate ellipse of the specified ring image, and by substituting the major axis and the minor axis of the approximate ellipse into a known equation, the spherical power, the astigmatic power, and the astigmatic axis angle (refraction). Force value) is calculated. Alternatively, the eye refractive power calculation unit 221 can obtain the parameter of the eye refractive power based on the deformation and displacement of the ring image with respect to the reference pattern.

Further, the eye refractive power calculation unit 221 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 portion observation system 5. For example, the optical power calculation unit 221 calculates the radius of curvature of the cornea of the strong main meridian and the weak main meridian on the anterior surface of the cornea by analyzing the keratling image, and calculates the above parameter based on the radius of curvature of the cornea.

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

In order to improve the image quality, it is possible to superimpose (add and average) a plurality of data sets collected by repeating scanning with the same pattern multiple times.

(Data processing unit 223)
The data processing unit 223 performs various data processing (image processing) and analysis processing on the tomographic image formed by the image forming unit 222. For example, the data processing unit 223 executes correction processing such as image brightness correction and dispersion correction. Further, the data processing unit 223 performs various image processing and analysis processing on the image (anterior eye portion image and the like) obtained by using the anterior eye portion observation system 5.

The data processing unit 223 can form volume data (voxel data) of the eye E to be inspected 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 the volume data to form a pseudo three-dimensional image when viewed from a specific line-of-sight direction.

The data processing unit 223 includes an intraocular distance calculation unit 231, a determination unit 232, and a myopia progression estimation unit 233. The myopia progression estimation unit 233 includes a multivariate analysis unit 233A and a progression information generation unit 233B.

(Intraocular distance calculation unit 231)
The intraocular distance calculation unit 231 obtains one or more intraocular distances in the eye E to be inspected based on the detection result of the interference light LC obtained by the OCT optical system 8. For example, the intraocular distance calculation unit 231 analyzes the detection result of the interference light LC obtained by the OCT optical system 8 to determine the peak position of the detection result (interference signal) of the interference light corresponding to a predetermined portion in the eye. Identify and determine the above intraocular distance based on the distance between the identified peak positions. The intraocular distance calculation unit 231 can obtain at least the axial length and the choroidal film thickness. The intraocular distance calculation unit 231 according to some embodiments obtains the axial length, corneal thickness, anterior chamber depth, crystalline lens thickness, vitreous cavity length, retinal film thickness, choroidal film thickness, and the like.

The choroid thickness is at least one of the choroid thickness in the fovea, the average choroid near the fovea, the average choroid in each of the plurality of quadrants obtained by dividing the vicinity of the fovea, and the choroid around the macula. include. The average choroid near the fovea is, for example, the average choroid at two or more positions within a range of about φ2 centered on the fovea. The average choroid thickness in each of the plurality of quadrants obtained by dividing the vicinity of the fovea is, for example, the average choroid thickness at two or more positions in each quadrant by dividing the vicinity of the fovea into four quadrants. The choroid around the macula is, for example, the choroid near the equator.

(Judgment unit 232)
The determination unit 232 includes the refractive power value (measured value of the refractive power) obtained by the eye refractive power calculation unit 221, one or more intraocular distances obtained by the intraocular distance calculation unit 231, and information on the subject. And, based on the standard data, it is determined whether or not the eye E to be inspected has axial myopia. For example, the determination unit 232 extracts statistically valid data from the standard data based on the information of the subject, and determines the refractive power value and the intraocular distance of 1 or more with respect to the extracted data. Based on this, it is determined whether or not the eye E to be inspected has axial myopia. The subject information according to some embodiments includes the subject's age, gender, height, weight, and eye characteristic information of the subject's close relatives. Relatives are relatives within the second degree of kinship of the subject. Relatives are preferably the subject's father or mother. The ocular characteristic information includes the refractive power value (spherical power, astigmatic power and astigmatic axis angle, or equivalent spherical power). For example, it is possible to reflect in the determination result that it is more likely that the effect of suppressing myopia of a subject whose parents have myopia is higher than that of a subject whose parents have myopia. .. In some embodiments, the ocular property information further comprises at least one of axial length and choroid. In some embodiments, the subject's information is used as a parameter to a function described below, as well as the refractive power value and intraocular distance.

The subject information according to some embodiments further includes information regarding the subject's lifestyle. Information on lifestyle includes TV viewing status (viewing time zone, viewing time), usage status of personal computers and mobile devices (usage time zone, usage time), outing activity status (activity time zone, activity time), etc. be. Hereinafter, the case where the subject's information is mainly of age and gender will be described.

The determination unit 232 according to some embodiments determines whether or not the eye E to be inspected has axial myopia by comparing the refractive power value, the intraocular distance of 1 or more, and the information of the subject with the standard data. To judge. In this case, the determination unit 232 uses the obtained refractive power value, the intraocular distance of 1 or more, the information of the subject, the refractive power value in the normal eye, the intraocular distance of 1 or more, and the information of the subject. By comparing with the included standard data, it is possible to determine whether or not the eye E to be inspected has axial myopia.

For example, the determination unit 232 is obtained by the refractive power value of the normal eye extracted from the standard data corresponding to the information of the subject, the intraocular distance of 1 or more, the refractive power value obtained by the measurement, and the measurement. It is compared with one or more intraocular distances, and it is determined whether or not the eye E to be inspected has axial myopia based on the obtained plurality of differences. The determination unit 232 determines that the result of comparison between a predetermined one or more differences among the obtained plurality of differences and the threshold value, the absolute value of the predetermined difference among the plurality of differences, or the threshold value or more or the threshold value or less among the plurality of differences. It is possible to determine whether or not the eye E to be inspected has axial myopia based on the number of differences.

The determination unit 232 according to some embodiments has one or more correlation functions f (x ₁ , x ₂ , ..., X _n ) (x ₁ to x _n ) obtained by multivariate analysis of standard data. Determines whether or not the subject E is axial myopia based on the refractive power value, 1 or more intraocular distance, and at least one of the subject's information). Correlation functions according to the embodiment include a function represented by an equation obtained by multiple regression analysis and a function represented by an equation obtained by discriminant analysis.

For example, the determination unit 232 has a correlation function F (x ₁ , x ₂ , ..., X _n ) (x ₁ to x _n ) representing an estimated value of the axial length obtained by multivariate analysis. Estimated value of axial length obtained by substituting the age of the subject, etc. for the force value, one or more intraocular distance other than the axial length, and at least one of the subject's information). Based on the above, it is determined whether or not the eye E to be inspected has axial myopia.

For example, the determination unit 232 has a correlation function G (x ₁ , x ₂ , ..., X _n ) (x ₁ to x _n ) representing an estimated value of the choroid thickness as in the correlation function F. Use the choroid thickness estimate obtained by substituting the subject's age, etc. for one or more intraocular distances other than the thickness, at least one of the subject's information, and the correlation function F. It is determined whether or not the eye E to be examined has axial myopia based on the estimated value of the axial length.

The determination unit 232 also obtains the intraocular distance other than the axial length (for example, corneal thickness, anterior chamber depth, crystalline lens thickness, vitreous cavity length, retinal thickness, etc.) from one or more correlation functions similar to the axial length. It is possible to determine whether or not the eye E to be inspected has axial myopia based on one or more estimated values obtained.

The determination unit 232 according to some embodiments has an evaluation function H (x ₁ , x ₂ , ..., X _n ) (x ₁ to x _n ) obtained by multivariate analysis of standard data. It is determined whether or not the eye E to be inspected has axial myopia based on the force value, the intraocular distance of 1 or more, and at least one of the information of the subject). For example, the determination unit 232 determines whether or not the eye E to be inspected has axial myopia based on the evaluation value obtained by substituting the age of the subject into the evaluation function H.

The determination unit 232 according to some embodiments is learning generated by machine learning using the above standard data, eye measurement data diagnosed as axial myopia in the past, and information of the subject. Based on the output value obtained by substituting the age of the subject into the completed model, it is determined whether or not the eye E to be examined has axial myopia.

The determination unit 232 according to some embodiments is based on the above standard data, the measurement data of the eye diagnosed as axial myopia in the past, and the cluster analysis result using the information of the subject. By determining whether the refractive force value obtained by this measurement, the intraocular distance of 1 or more, and at least one of the information of the subject belongs to any of the data groups, the eye E to be examined is axial myopia. Determine if it exists.

The determination result by the determination unit 232 according to the embodiment includes information indicating whether or not the eye E to be inspected has axial myopia. The determination unit 232 according to some embodiments is not only information indicating whether or not the eye E to be inspected has axial myopia, but also how close it is to the determination criteria for determining whether or not the eye is axial myopia. The information indicating that is output. In this case, the determination unit 232 obtains the difference between the obtained estimated value or output value and the reference value corresponding to the determination standard, and generates information indicating how close to the determination standard according to the difference. It is possible.

(Myopia progression estimation unit 233)
The myopia progression estimation unit 233 includes a refractive power value (measured value of refractive power) obtained by the eye refractive power calculation unit 221, an intraocular distance of 1 or more obtained by the intraocular distance calculation unit 231, and a subject. Information on the progression of axial myopia of the eye E to be inspected is generated based on the information of the above and standard data. The progress information according to some embodiments is information indicating to what extent axial myopia has progressed at the time of measurement. The progress information according to some embodiments is information indicating to what extent axial myopia progresses at a predetermined time point after the measurement time point. Progress information according to some embodiments includes estimates of intraocular parameters such as refractive power values and axial lengths at predetermined time points after the measurement time point. That is, the progress information of axial myopia according to some embodiments is the refractive power value after the measurement timing of at least one of the refractive power value and the intraocular distance of 1 or more and at least one of the intraocular distance of 1 or more. Includes estimates.

(Multivariate analysis unit 233A)
The multivariate analysis unit 233A acquires a correlation function J (x ₁ , x ₂ , ..., X _n ) representing an estimated value of the axial length by performing multivariate analysis of standard data. In the correlation function J shown in the equation (1), x ₁ to x _n are at least one of the refractive power value, one or more intraocular distance other than the axial length, and the subject's information, and a ₀ is a constant. ₁ to an are _coefficients .

J (x ₁ , x ₂ , ..., x _n ) = a ₀ + a ₁ x ₁ + a ₂ x ₂ + ... + an _n x _n
... (1)

For example, the multivariate analysis unit 233A has an optical power value of the eye E to be inspected, an intraocular distance of 1 or more other than the axial length, and information on the subject (subject) with respect to the correlation function J shown in the equation (1). By inputting (including the desired age of the examiner), an estimated value of the axial length of the eye to be inspected E in the future is obtained. The multivariate analysis unit 233A can estimate the future progression of axial myopia of the eye E to be inspected based on the acquired estimated value of the axial length.

Further, the multivariate analysis unit 233A acquires a correlation function K (x ₁ , x ₂ , ..., X _n ) representing an estimated value of the refractive power value by performing multivariate analysis of standard data. In the correlation function K shown in the equation (2), x ₁ to x _n are at least one of the intraocular distance of 1 or more and the information of the subject, b ₀ is a constant, and b ₁ to b _n . Is a coefficient.

K (x ₁ , x ₂ , ..., x _n ) = b ₀ + b ₁ x ₁ + b ₂ x ₂ + ... + b _n x _n
... (2)

For example, the multivariate analysis unit 233A has an intraocular distance of 1 or more in the eye E to be inspected and information on the subject (including the desired age of the subject) with respect to the correlation function K shown in the equation (2). Is input to obtain an estimated value of the refractive power value of the eye to be inspected E in the future. The multivariate analysis unit 233A can estimate the degree of progression of axial myopia in the future of the eye E to be inspected based on the obtained estimated value of the refractive power value.

The multivariate analysis unit 233A according to some embodiments acquires a correlation function J1 (x ₁ , x ₂ , ..., X _n ) representing an estimated value of the axial length by performing multivariate analysis of standard data. do. In the correlation function J1 shown in the equation (3), x ₁ to x _n are two or more refractive power values obtained at different measurement timings and two or more other than the axial lengths obtained at different measurement timings. The intraocular distance of 1 or more and at least one of the subject's information, c ₀ is a constant, and _{c 1} to cn are coefficients.

J1 (x ₁ , x ₂ , ..., x _n ) = c ₀ + c ₁ x ₁ + c ₂ x ₂ + ... + c _n x _n
... (3)

For example, the multivariate analysis unit 233A acquires an estimated value of the axial length of the eye to be inspected E in the future from the correlation function J1 shown in the equation (3). Thereby, it is possible to obtain an estimated value of the axial length of the eye E to be inspected at a desired age based on the change in the refractive power value, the change in the axial length, and the information of the subject. In this case, it is possible to obtain a highly reliable estimated value of the axial length as compared with the case of using the correlation function J shown in the equation (1).

The multivariate analysis unit 233A according to some embodiments acquires a correlation function K1 (x ₁ , x ₂ , ..., X _n ) representing an estimated value of the refractive power value by performing multivariate analysis of standard data. do. In the correlation function K1 shown in the equation (4), x ₁ to x _n are two or more refractive power values obtained at different measurement timings, and two or more intraocular distances of two or more obtained at different measurement timings. Is at least one of the measured value of the subject and the information of the subject, d ₀ is a constant, and d ₁ to d _n are coefficients.

K1 (x ₁ , x ₂ , ..., x _n ) = d ₀ + d ₁ x ₁ + d ₂ x ₂ + ... + d _n x _n
... (4)

For example, the multivariate analysis unit 233A acquires an estimated value of the refractive power value of the future eye E to be inspected from the correlation function K1. Thereby, it is possible to obtain an estimated value of the refractive power value of the eye E to be inspected at a desired age based on the change in the refractive power value, the change in the axial length, and the information of the subject. In this case, it is possible to obtain a highly reliable estimated value of the refractive power value as compared with the case of using the correlation function K shown in the equation (2).

The correlation functions J, K, J1, and K1 are not limited to the formats shown in the equations (1) to (4), and may be any function.

(Progress information generation unit 233B)
The progress information generation unit 233B extracts analysis information corresponding to the information of the subject from the multivariate analysis result by the multivariate analysis unit 233A, and generates progress information based on the extracted analysis information. The progress information generation unit 233B generates progress information, for example, with the age as the horizontal axis and the parameter representing the progress of axial myopia as the vertical axis.

For example, the progress information generation unit 233B generates progress information including an estimated value of the axial length at a desired age of the subject based on the function value obtained by using the above-mentioned correlation function J or the correlation function J1. do. For example, the progress information generation unit 233B generates progress information including an estimated value of the refractive power value at a desired age of the subject based on the function value obtained by using the above-mentioned correlation function K or the correlation function K1. do. The progress information generation unit 233B according to some embodiments generates progress information including an estimated value of a plurality of axial lengths or an estimated value of a plurality of refractive power values after a desired age.

(Display unit 270, operation unit 280)
The display unit 270, as a user interface unit, displays information under the control of the control unit 210. The display unit 270 includes the 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 device. The operation unit 280 includes various hardware keys (joysticks, buttons, switches, etc.) provided in the ophthalmic apparatus. Further, the operation unit 280 may include various software keys (buttons, icons, menus, etc.) displayed on the touch panel type display screen 10a.

At least a part of the display unit 270 and the operation unit 280 may be integrally configured. As a typical example thereof, there is a touch panel type 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 includes a communication interface according to the connection form with the external device. An example of an external device is a spectacle lens measuring device for measuring the optical characteristics of a lens. The spectacle lens measuring device measures the power of the spectacle lens worn by the subject, and inputs this measurement data to the ophthalmic device 1000. Further, the external device may be an arbitrary ophthalmic device, a device (reader) for reading information from a recording medium, a device (writer) for writing information on a recording medium, or the like. Further, 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, for example, the processing unit 9.

The reflex measurement optical system (refraction measurement projection system 6 and reflex measurement light receiving system 7) and the ocular refractive power calculation unit 221 are examples of the “refractive power measurement unit” according to the embodiment. The OCT optical system 8 and the intraocular distance calculation unit 231 are examples of the “intraocular distance measuring unit” according to the embodiment. The data processing unit 223 is an example of the "analysis unit" according to the embodiment. The correlation functions J and K are examples of "first analysis information" obtained in advance using at least one of the refractive power of the eye, one or more intraocular distances, and the information of the person to be measured as variables based on standard data. be. The correlation functions J1 and K1 are at least one of the refractive power of the eye and the change in the refractive power, the change in the intraocular distance of 1 or more and the intraocular distance of 1 or more, and the information of the person to be measured based on the standard data. Is an example of the "second analysis information" obtained in advance with the above as a variable.

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

FIG. 5 shows an example of the operation of the ophthalmic apparatus 1000. FIG. 5 shows a flow chart of an operation example of the ophthalmic apparatus 1000. The storage unit 212 stores a computer program for realizing the process shown in FIG. The main control unit 211 executes the process shown in FIG. 5 by operating according to this computer program. Here, it is assumed that the information of the subject is stored in the storage unit 212 in advance.

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

Specifically, the main control unit 211 turns on the Z alignment light source 11 and the XY alignment light source 21. Further, the main control unit 211 turns on the front eye portion illumination light source 50. The processing unit 9 acquires an image pickup signal of the front eye portion image on the image pickup surface of the image pickup element 59, and causes the display unit 270 to display the front eye portion image. After that, the optical system shown in FIG. 1 is moved to the inspection position of the eye E to be inspected. The inspection position is a position where the inspection of the eye E to be inspected can be performed within sufficient accuracy. The eye E to be inspected is placed at the examination position via the above-mentioned alignment (alignment by the Z alignment system 1 and the XY alignment system 2 and the anterior eye observation system 5). The 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 examination position of the eye E to be inspected and the preparation for performing the objective measurement are performed.

Further, the main control unit 211 moves the reflex measurement light source 61, the focusing lens 74, and the fixative unit 40 (liquid crystal panel 41) to the position of the origin (for example, the position corresponding to 0D) along the respective optical axes. Move it.

The kerato measurement may be executed after the alignment in step S1 is completed. In this case, the main control unit 211 causes the liquid crystal panel 41 to display a pattern indicating the fixative at the display position corresponding to the desired fixative position. As a result, the eye E to be inspected is gazed at a desired fixative position. After that, the main control unit 211 turns on the keratling light source 32. When light is output from the keratling light source 32, a ring-shaped light flux for measuring the shape of the cornea is projected onto the cornea Cr of the eye E to be inspected. The ocular refractive power calculation unit 221 calculates the corneal radius of curvature by performing arithmetic processing on the image acquired by the image pickup element 59, and the corneal refractive power, corneal astigmatism, and corneal astigmatism are calculated from the calculated corneal radius of curvature. Calculate the axis angle. In the control unit 210, the calculated corneal refractive power and the like are stored in the storage unit 212.

The operation of the ophthalmic apparatus 1000 shifts to step S2 by the instruction from the main control unit 211 or the user's operation or instruction to the operation unit 280.

(S2: Measurement of refractive power)
In the refractive power measurement, the main control unit 211 projects a ring-shaped measurement pattern luminous flux for measuring the refractive power onto the eye E to be inspected as described above. A ring image based on the return light of the measurement pattern luminous flux from the eye E to be inspected is formed on the image pickup surface of the image pickup element 59. The main control unit 211 determines whether or not a ring image based on the return light from the fundus Ef detected by the image sensor 59 could be 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 image sensor 59, and whether the width of the image (difference between the outer diameter and the inner diameter) is equal to or more than a predetermined value. Judge whether or not. Alternatively, the main control unit 211 determines whether or not a ring image can be acquired by determining whether or not a ring can be formed based on a point (image) having a predetermined height (ring diameter) or more. May be good.

When it is determined that the ring image can be obtained, the optical power calculation unit 221 analyzes the ring image based on the return light of the measurement pattern luminous flux projected on the eye E to be inspected by a known method, and analyzes the provisional spherical power S and the tentative spherical power S. A tentative astigmatic power C is obtained. Based on the obtained temporary spherical power S and astigmatic power C, the main control unit 211 sets the reflex measurement light source 61, the focusing lens 74, and the fixative unit 40 (liquid crystal panel 41) into equivalent spherical power (S + C / 2). Move to the position of (the position corresponding to the temporary far point). The main control unit 211 further moves the fixative unit 40 (liquid crystal panel 41) from that position to the cloud fog position, and then controls the reflex measurement projection system 6 and the reflex measurement light receiving system 7 as the main measurement to obtain a ring image. Get it again. The main control unit 211 causes the eye refractive power calculation unit 221 to calculate the spherical power, the astigmatic power, and the astigmatic 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.

Further, the eye refractive power calculation unit 221 obtains a position corresponding to the far point of the eye E to be inspected (a position corresponding to the far point obtained by this measurement) from the obtained spherical power and astigmatic power. The main control unit 211 moves the liquid crystal panel 41 to a position corresponding to the obtained far point. In the control unit 210, the position of the focusing lens 74, the calculated spherical power, and the like are stored in the storage unit 212. The operation of the ophthalmic apparatus 1000 shifts to step S3 by the instruction from the main control unit 211 or the user's operation or instruction to the operation unit 280.

When it is determined that the ring image cannot be acquired, the main control unit 211 considers the possibility of an intensified refractive error eye and sets the reflex measurement light source 61 and the focusing lens 74 on the minus power side (for example, in a preset step). -10D), move to the plus frequency side (for example, + 10D). The main control unit 211 detects the ring image at each position by controlling the reflex measurement light receiving system 7. When it is determined that the ring image cannot be acquired even after that, the main control unit 211 executes a predetermined measurement error process. At this time, the operation of the ophthalmic apparatus 1000 may shift to step S3. In the control unit 210, information indicating that the reflex measurement result was not obtained is stored in the storage unit 212.

(S3: OCT measurement)
First, the main control unit 211 moves the fixative unit 40 (liquid crystal panel 41) from the cloud fog position to the in-focus position. In some embodiments, the in-focus position maximizes the intensity of the interference signal or the like from 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). It is a position adjusted so as to be.

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

(S4: Calculate the intraocular distance)
The main control unit 211 causes the intraocular distance calculation unit 231 to calculate an intraocular distance of 1 or more from the detection result of the interference light obtained in step S3 or the tomographic image of the fundus Ef. The intraocular distance calculation unit 231 calculates the axial length, corneal thickness, anterior chamber depth, crystalline lens thickness, vitreous cavity length, retinal film thickness, choroidal film thickness, and the like.

(S5: Axial myopia determination)
Next, the main control unit 211 includes the refractive power value obtained in step S2, the intraocular distance of 1 or more obtained in step S4, and the information and standard data of the subject stored in the storage unit 212. Based on the above, the determination unit 232 determines whether or not the eye E to be inspected has axial myopia. The determination unit 232 determines whether or not the eye E to be inspected has axial myopia as described above.

(S6: Generate progress information)
Further, the main control unit 211 uses the refractive power value obtained in step S2, the intraocular distance of 1 or more obtained in step S4, and the information and standard data of the subject stored in the storage unit 212. Based on this, the myopia progression estimation unit 233 is generated with the progression information of the axial myopia of the eye E to be inspected. The myopia progression estimation unit 233 generates information on the progression of axial myopia of the eye E to be inspected as described above.

(S7: Display)
Subsequently, the main control unit 211 causes the display unit 270 to display the information corresponding to the determination result of the determination unit 232 obtained in step S5 and the progress information of axial myopia obtained in step S6.

FIG. 6 schematically shows a display example of the display unit 270 according to the embodiment.

For example, the main control unit 211 corresponds to the refractive power value RES1 acquired in step S2, the intraocular distance RES2 obtained in step S4 or more, and the determination result of the determination unit 232 obtained in step S5. The information DT, the progress information GP1 of axial myopia obtained in step S6, and the future estimated value PI of the refractive power value and the axial length are displayed. The estimated value PI can be generated from the progress information GP1. In FIG. 6, the information DT corresponding to the determination result that the eye E to be inspected is not axial myopia is displayed. As the progress information GP1, there are an estimated value of the axial length and the refractive power value after a desired age, a graph showing a time change of the estimated value of the axial length and the refractive power value, and the like.

This completes the operation of the ophthalmic apparatus 1000 (end).

FIG. 5 shows an operation example in which the determination of axial myopia and the progress information of axial myopia are generated based on the measured values and the measured values obtained by one-time refractive power measurement and OCT measurement. However, the operation of the ophthalmic apparatus 1000 according to the embodiment is not limited to the flow shown in FIG.

FIG. 7 shows another example of the operation of the ophthalmic apparatus 1000. FIG. 7 shows a flow chart of an operation example of the ophthalmic apparatus 1000, similarly to FIG. The storage unit 212 stores a computer program for realizing the process shown in FIG. 7. The main control unit 211 executes the process shown in FIG. 7 by operating according to this computer program. Here, it is assumed that the information of the subject, the measured value of the refractive power measurement obtained by the flow shown in FIG. 5, and the measured value of the OCT measurement are stored in advance in the storage unit 212. In FIG. 7, detailed description of the same portion as in FIG. 5 will be omitted.

(S11: Alignment)
The main control unit 211 executes alignment in the same manner as in step S1. In some embodiments, the alignment is performed using the alignment information obtained at the time of the previous measurement such as the refractive power value.

(S12: Measurement of refractive power)
The main control unit 211 executes the refractive power measurement in the same manner as in step S2. In some embodiments, the positional relationship of the optical system for performing the refractive power measurement is changed based on the position information of the optical system obtained at the time of the previous measurement of the refractive power.

(S13: OCT measurement)
The main control unit 211 executes OCT measurement in the same manner as in step S3. In some embodiments, the positional relationship of the optical system for performing the OCT measurement is changed based on the position information of the optical system obtained at the time of the previous OCT measurement.

(S14: Calculate the intraocular distance)
Similar to step S4, the main control unit 211 causes the intraocular distance calculation unit 231 to calculate one or more intraocular distances from the detection result of the interference light obtained in step S13 or the tomographic image of the fundus Ef. The intraocular distance calculation unit 231 calculates at least the same intraocular distance as at the time of the previous intraocular distance calculation. Here, the intraocular distance calculation unit 231 calculates the axial length, corneal thickness, anterior chamber depth, crystalline lens thickness, vitreous cavity length, retinal film thickness, and choroidal film thickness. Further, the intraocular distance calculation unit 231 calculates these changes with time.

(S15: Axial myopia determination)
Similar to step S5, the main control unit 211 includes the refractive power value obtained in step S12, the intraocular distance of 1 or more obtained in step S14, and the information of the subject stored in the storage unit 212. Based on the standard data, the determination unit 232 determines whether or not the eye E to be inspected has axial myopia.

(S16: Progress analysis)
The main control unit 211 has, for example, the above-mentioned correlation function J1, the refractive power value obtained by the previous measurement stored in the storage unit 212, the intraocular distance of 1 or more, and the refractive power obtained by this measurement. By substituting the value and the intraocular distance of 1 or more, the estimated value of the axial length of the eye to be inspected E in the future is obtained. The main control unit 211, for example, has the above-mentioned correlation function K1 the refractive power value obtained by the previous measurement stored in the storage unit 212, the intraocular distance of 1 or more, and the refractive power obtained by this measurement. By substituting the value and the intraocular distance of 1 or more, the estimated value of the refractive power value of the eye to be inspected E in the future is obtained.

(S17: Generate progress information)
The main control unit 211 includes the refractive power value and its change obtained in step S12, the intraocular distance of one or more obtained in step S14 and its change, and the subject's information and standard data stored in the storage unit 212. Based on the above, the progress information of the axial myopia of the eye E to be inspected is output to the myopia progress estimation unit 233.

(S18: Display)
The main control unit 211 causes the display unit 270 to display the information corresponding to the determination result of the determination unit 232 obtained in step S15 and the progress information of axial myopia obtained in step S17.

8 and 9 schematically show the progress information GP1 displayed on the display unit 270 according to the embodiment. FIG. 8 shows an example of the progress information generated in step S6. FIG. 9 shows an example of the progress information generated in step S17.

For example, as shown in FIG. 8, the main control unit 211, together with the future change characteristic Q1 of the axial length and the future change characteristic Q2 of the refractive power value based on the standard data, is based on the age of the current subject. The display unit 270 displays the change characteristic Q10 of the estimated value of the future axial length and the change characteristic Q11 of the estimated value of the future refractive power value (spherical power). By representing the change characteristics Q1 and Q2 with a solid line and the change characteristics Q10 and Q11 with a broken line, it is possible to easily recognize future changes in the axial length and the refractive power value with respect to the measurement time point.

For example, as shown in FIG. 9, the main control unit 211 sets the measured value of two or more axial lengths together with the future change characteristic Q1 of the axial length and the future change characteristic Q2 of the refractive power value based on the standard data. The display unit 270 displays the change characteristic Q10'of the estimated value of the future axial length based on the change characteristic Q10'and the change characteristic Q11'of the estimated value of the future refractive power value based on the measured value of the refractive power value (spherical power) of 2 or more. .. By representing the change characteristics Q1 and Q2 with a solid line and the change characteristics Q10'and Q11' with a broken line, it is possible to easily recognize future changes in the axial length and the refractive power value.

Although the estimated values of the future axial length and the refractive power value have been described in FIGS. 8 and 9, the main control unit 211 has a future corneal thickness, anterior chamber depth, crystalline lens thickness, vitreous cavity length, and retinal thickness. Similarly, the estimated value of the choroid film thickness can be displayed on the display unit 270.

As described above, according to the embodiment, it is determined whether or not the eye E to be inspected has axial myopia from the information obtained by the refractive power measurement and the OCT measurement based on the standard data. It is possible to improve the reliability of progress prediction. Further, according to the embodiment, since the progress information of the axial myopia of the eye E to be inspected is generated from the information obtained by the refractive power measurement and the OCT measurement based on the standard data, the reliability of the prediction of the progress of myopia is reliable. Can be improved.

In some embodiments, based on the refractive power value, an intraocular distance of 1 or more, corneal shape information obtained by kerato measurement, accommodation tremor measurement value, myopia measurement, blood flow information, etc. It determines whether or not it is axial myopia, and generates information on the progress of axial myopia.

In some embodiments, it is determined whether the eye E to be inspected is axial myopia or refractive myopia from the refractive power value, the intraocular distance of 1 or more, and the information of the subject. In some embodiments, it is determined whether or not it is refractive myopia from the age determined to be myopia, the number of years since it was determined to be myopia, and changes in corneal shape (thickness) and lens thickness.

[Action / Effect]
The operation and effect of the ophthalmic appliance according to the embodiment will be described.

The ophthalmic apparatus (1000) according to some embodiments includes a refractive power measuring unit (ref measuring projection system 6, reflex measuring light receiving system 7, and ocular refractive power calculation unit 221) and an intraocular distance measuring unit (OCT optical system). 8. It includes an intraocular distance calculation unit 231), a storage unit (212), and an analysis unit (data processing unit 223). The refractive power measuring unit acquires the measured value of the refractive power of the eye to be inspected (E). The intraocular distance measuring unit acquires a measured value of one or more intraocular distances in the eye to be inspected. The storage unit stores in advance standard data (normalative data) in which the information of the subject is associated with the refractive power of the eye of the subject who is a normal eye and the intraocular distance of 1 or more. The analysis unit uses the measured value of the refractive power acquired by the refractive power measuring unit, the measured value of one or more intraocular distances acquired by the intraocular distance measuring unit, the information of the subject, and the standard data. Based on this, it is determined whether or not the eye to be inspected has axial myopia.

According to such a configuration, whether the eye to be inspected has axial myopia based on the measured value of the refractive power of the eye to be inspected, the measured value of the intraocular distance of 1 or more, the information of the subject, and the standard data. Since it is determined whether or not it is, the reliability of determining whether or not it is axial myopia can be improved. As a result, it becomes possible to predict the progression of axial myopia with higher reliability.

In the ophthalmic apparatus according to some embodiments, the analysis unit focuses on the eye to be inspected by comparing the measured value of the refractive power, the measured value of the intraocular distance of 1 or more, and the information of the subject with the standard data. Determine if you have sexual myopia.

According to such a configuration, it is determined whether or not the subject's eye has axial myopia by using the measured values of the refractive power and the intraocular distance of 1 or more and the comparison result between the subject's information and the standard data. Therefore, it is possible to determine highly reliable axial myopia with a simple process.

The ophthalmic appliance according to some embodiments is a control for displaying information corresponding to a determination result indicating whether or not the eye to be inspected obtained by the analysis unit is axial myopia on the display means (display units 10, 270). (210, main control unit 211) is included.

With such a configuration, it becomes possible to easily take measures such as calling attention, proposing myopia suppression, recommending regular medical examinations, and reviewing lifestyle habits.

In the ophthalmic apparatus according to some embodiments, the analysis unit obtains in advance the refractive power of the eye, one or more intraocular distances, and at least one of the information of the person to be measured as variables based on standard data. 1 By referring to the analysis information, progress information of axial myopia is generated.

According to such a configuration, the progress of axial myopia and the future progress can be determined by a relatively simple process for a measured value of an arbitrary refractive power, an intraocular distance of 1 or more, and information of the subject. It will be possible to present it to the subject.

The ophthalmic apparatus (1000) according to some embodiments includes a refractive power measuring unit (ref measuring projection system 6, reflex measuring light receiving system 7, and ocular refractive power calculation unit 221) and an intraocular distance measuring unit (OCT optical system). 8. It includes an intraocular distance calculation unit 231), a storage unit (212), and an analysis unit (data processing unit 223). The refractive power measuring unit acquires the measured value of the refractive power of the eye to be inspected (E). The intraocular distance measuring unit acquires a measured value of one or more intraocular distances in the eye to be inspected. The storage unit stores in advance standard data in which the information of the subject is associated with the refractive power of the eye of the subject who is a normal eye and the intraocular distance of 1 or more. The analysis unit uses the measured value of the refractive power acquired by the refractive power measuring unit, the measured value of one or more intraocular distances acquired by the intraocular distance measuring unit, the information of the subject, and the standard data. Based on this, information on the progress of axial myopia in the subject eye is generated.

According to such a configuration, the progress information of the axial myopia of the inspected eye is based on the measured value of the refractive power of the inspected eye, the measured value of the intraocular distance of 1 or more, the information of the subject, and the standard data. Therefore, the reliability of the prediction of axial myopia can be improved.

In the ophthalmic apparatus according to some embodiments, the analysis unit acquires two or more refractive force measurement values acquired by the refractive force measurement unit at different measurement timings and the intraocular distance measurement unit at different measurement timings. Based on the above-mentioned two or more measurements of the intraocular distance, the subject's information, and the standard data, the progress information of the axial myopia of the subject's eye is generated.

According to such a configuration, it is possible to generate information indicating the progress and future progress of axial myopia by taking into account the change in the measured value of the refractive power and the change in the measured value of the intraocular distance of 1 or more. Therefore, the reliability of the prediction of axial myopia can be further improved.

The ophthalmic apparatus (1000) according to some embodiments includes a refractive power measuring unit (ref measuring projection system 6, reflex measuring light receiving system 7, and ocular refractive power calculation unit 221) and an intraocular distance measuring unit (OCT optical system). 8. It includes an intraocular distance calculation unit 231), a storage unit (212), and an analysis unit (data processing unit 223). The refractive power measuring unit acquires the measured value of the refractive power of the eye to be inspected (E). The intraocular distance measuring unit acquires a measured value of one or more intraocular distances in the eye to be inspected. The storage unit stores in advance standard data in which the information of the subject is associated with the refractive power of the eye of the subject who is a normal eye and the intraocular distance of 1 or more. The analysis unit has two or more measurement values of refractive force acquired by the refractive force measurement unit at different measurement timings and two or more above-mentioned intraocular distances acquired by the intraocular distance measurement unit at different measurement timings. Based on the measured values, the subject's information, and the standard data, the progress information of the axial myopia of the subject's eye is generated.

According to such a configuration, the axis of the eye to be inspected is based on the measured value of the refractive power of the eye to be inspected, the measured value of one or more intraocular distances, these changes, the information of the subject, and the standard data. Since the information indicating the progress of sexual myopia and the future progress is generated, the reliability of the prediction of axial myopia can be improved.

In the ophthalmic apparatus according to some embodiments, the analysis unit determines the refractive power of the eye and the change in the refractive power, the change in the intraocular distance of 1 or more and the change in the intraocular distance of 1 or more, and the subject, based on the standard data. By referring to the second analysis information obtained in advance with at least one of the information of the measurer as a variable, the progress information of axial myopia is generated.

According to such a configuration, the progress of axial myopia and the future can be performed with relatively simple processing for arbitrary refractive power, measured values of one or more intraocular distances, changes thereof, and information of the subject. It becomes possible to present the progress of the above to the subject or the like.

In the ophthalmic apparatus according to some embodiments, the progress information includes an estimated value of the refractive power after at least one measurement timing of the refractive power and one or more intraocular distances and at least one of the intraocular distances of one or more. ..

With such a configuration, it becomes possible to present to the examiner and the examinee in an easy-to-understand manner the degree of progress of axial myopia of the eye to be inspected and the time change of the future progress.

The ophthalmic apparatus according to some embodiments includes a control unit (210, main control unit 211) for displaying the progress information obtained by the analysis unit on the display means (display units 10, 270).

With such a configuration, it becomes possible to easily take measures such as calling attention, proposing myopia suppression, recommending regular medical examinations, and reviewing lifestyle habits.

In an ophthalmic appliance according to some embodiments, the subject's information and the subject's information include age and gender.

According to such a configuration, the accuracy of determining whether or not the subject has axial myopia is improved, and the accuracy of the progress information of the axial myopia is improved, in consideration of the age and gender of the subject. Will be possible.

In the ophthalmic apparatus according to some embodiments, the subject's information includes eye characteristic information of the subject's close relatives.

According to such a configuration, it is possible to improve the accuracy of determining whether or not the subject has axial myopia and improve the accuracy of the progress information of axial myopia in consideration of the genetic information of the subject. become.

In an ophthalmic apparatus according to some embodiments, one or more intraocular distances include axial length and choroidal thickness.

According to such a configuration, the accuracy of determining whether or not the person has axial myopia can be improved by considering the axial length and the choroid, which are considered to have a high correlation with the axial myopia. It is possible to improve the accuracy of myopia progress information.

In some embodiments, the choroid is the choroid in the fovea, the average choroid near the fovea, the average choroid in each of the multiple quadrants obtained by dividing the fovea, and around the macula. Includes at least one of the choroidal thicknesses.

According to such a configuration, in consideration of the choroid film thickness which is considered to have a high correlation with axial myopia, the accuracy of determining whether or not it is axial myopia can be improved, and the progress information of axial myopia can be obtained. It is possible to improve the accuracy.

In the ophthalmic apparatus according to some embodiments, the intraocular distance measuring unit divides the light (L0) from the light source (OCT light source 101) into a reference light (LR) and a measurement light (LS), and divides the measurement light into a reference light (LR) and a measurement light (LS). Based on the OCT optical system (8) that projects to the eye to be inspected and detects the interference light (LC) between the return light of the measurement light from the eye to be inspected and the reference light, and the detection result of the interference light obtained by the OCT optical system. It includes an intraocular distance calculation unit (231) for obtaining an intraocular distance of 1 or more.

According to such a configuration, since the intraocular distance of 1 or more is obtained based on the measurement result obtained by the OCT measurement using the OCT optical system, the accuracy of the measured value is improved to achieve axial myopia. It is possible to improve the accuracy of determining whether or not the condition is true, and to improve the accuracy of the progress information of axial myopia.

Some embodiments are ophthalmic information processing programs for causing a computer to perform acquisition steps and analysis steps. The acquisition step acquires the measured value of the refractive power of the eye to be inspected (E), the measured value of one or more intraocular distances in the eye to be inspected, and the information of the subject. The analysis step includes the measured value of the refractive force acquired in the acquisition step, the measured value of the intraocular distance of 1 or more, and the information of the subject, and the refractive force of the eye of the subject who is a normal eye and 1 or more. It is determined whether or not the eye to be inspected has axial myopia based on the standard data in which the information of the subject is associated with the intraocular distance.

Here, "acquisition of measured value" means acquisition of the measured value by the refractive power measurement, or acquisition of the measured value obtained by the past refractive power measurement from a storage means or the like. According to such a program, whether the eye to be inspected has axial myopia based on the measured values of the refractive power of the eye to be inspected, the measured values of the intraocular distance of 1 or more, the information of the subject, and the standard data. Since it is determined whether or not it is, the reliability of determining whether or not it is axial myopia can be improved. As a result, it becomes possible to predict the progression of axial myopia with higher reliability.

In an ophthalmic information processing program according to some embodiments, the analysis step is to compare the measured value of refractive power, the measured value of one or more intraocular distances, and the subject's information with standard data. Determine if it is axial myopia.

According to such a program, it is determined whether or not the subject has axial myopia by using the measured values of the refractive power and the intraocular distance of 1 or more and the comparison result between the subject's information and the standard data. Therefore, it is possible to determine highly reliable axial myopia with a simple process.

The ophthalmic information processing program according to some embodiments displays information corresponding to the determination result indicating whether or not the eye to be inspected is axial myopia obtained in the analysis step on the display means (display units 10, 270). Includes control steps to cause.

Such a program makes it easy to take measures such as alerting, proposing myopia suppression, recommending regular medical examinations, and reviewing lifestyle habits.

Some embodiments are ophthalmic information processing programs for causing a computer to perform acquisition steps and analysis steps. The acquisition step acquires the measured value of the refractive power of the eye to be inspected (E), the measured value of one or more intraocular distances in the eye to be inspected, and the information of the subject. The analysis step includes the measured value of the refractive force acquired in the acquisition step, the measured value of the intraocular distance of 1 or more, the information of the subject, the refractive force of the eye of the subject who is a normal eye, and 1 or more. Generates information on the progression of axial myopia of the subject's eye based on standard data in which the subject's information is associated with the intraocular distance.

Here, "acquisition of measured value" means acquisition of the measured value by the refractive power measurement, or acquisition of the measured value obtained by the past refractive power measurement from a storage means or the like. According to such a program, the progress information of axial myopia of the subject eye is based on the measured value of the refractive power of the subject eye, the measured value of the intraocular distance of 1 or more, the information of the subject, and the standard data. Therefore, the reliability of the prediction of axial myopia can be improved.

In the ophthalmic information processing program according to some embodiments, the analysis step is a measurement value of two or more refractive powers acquired in the acquisition step at different measurement timings, and two or more measurement values of the above-mentioned intraocular distance. Generates information on the progression of axial myopia of the subject's eye based on the subject's information and standard data.

According to such a program, the change in the measured value of the refractive power and the change in the measured value of the intraocular distance of 1 or more are taken into consideration to generate information indicating the progress and future progress of axial myopia. Therefore, the reliability of the prediction of axial myopia can be further improved.

Some embodiments are ophthalmic information processing programs for causing a computer to perform acquisition steps and analysis steps. The acquisition step acquires the measured value of the refractive power of the eye to be inspected (E), the measured value of one or more intraocular distances in the eye to be inspected, and the information of the subject. The analysis step includes two or more measurement values of refractive force acquired in the acquisition step at different measurement timings, two or more measurement values of the above-mentioned intraocular distance, information on the subject, and a normal eye subject. Information on the progression of axial myopia of the subject's eye is generated based on standard data in which the information of the subject is associated with the refractive force of the eye of the measurer and one or more intraocular distances.

Here, "acquisition of measured value" means acquisition of the measured value by the refractive power measurement, or acquisition of the measured value obtained by the past refractive power measurement from a storage means or the like. According to such a program, the axis of the eye to be inspected is based on the measured values of the refractive power of the eye to be inspected and the measured values of one or more intraocular distances, these changes, the information of the subject, and the standard data. Since the information indicating the progress of sexual myopia and the future progress is generated, the reliability of the prediction of axial myopia can be improved.

In an ophthalmic information processing program according to some embodiments, the progress information is an estimate of at least one of the refractive power and one or more intraocular distances after the measurement timing of at least one of the refractive power and one or more intraocular distances. including.

According to such a program, it becomes possible to present to the examiner and the subject in an easy-to-understand manner the degree of progression of axial myopia of the eye to be inspected and the time change of the future progress.

The ophthalmic information processing program according to some embodiments includes a control step for displaying the progress information obtained in the analysis step on the display means (display units 10, 270).

Such a program makes it easy to take measures such as alerting, proposing myopia suppression, recommending regular medical examinations, and reviewing lifestyle habits.

In an ophthalmic information processing program according to some embodiments, the subject's information and the subject's information include age and gender.

According to such a program, the accuracy of determining whether or not the subject has axial myopia is improved, and the accuracy of the progress information of the axial myopia is improved, considering the age and gender of the subject. Will be possible.

In an ophthalmic information processing program according to some embodiments, the subject's information includes eye characteristic information of the subject's close relatives.

According to such a program, it is possible to improve the accuracy of determining whether or not the subject has axial myopia and improve the accuracy of the progress information of axial myopia in consideration of the genetic information of the subject. become.

In an ophthalmic information processing program according to some embodiments, an intraocular distance of one or more includes an axial length and a choroid.

According to such a program, the accuracy of determining whether or not the person has axial myopia can be improved by considering the axial length and the choroid, which are considered to have a high correlation with the axial myopia. It is possible to improve the accuracy of myopia progress information.

In some embodiments, the choroid is the choroid in the fovea, the average choroid near the fovea, the average choroid in each of the multiple quadrants obtained by dividing the fovea, and around the macula. Includes at least one of the choroidal thicknesses.

According to such a program, the choroid thickness, which is considered to have a high correlation with axial myopia, can be taken into consideration to improve the accuracy of determining whether or not it is axial myopia, and information on the progress of axial myopia can be obtained. It is possible to improve the accuracy.

<Others>
The embodiments shown above are merely examples for carrying out the present invention. A person who intends to carry out the present invention can make arbitrary modifications, omissions, additions, etc. within the scope of the gist of the present invention.

In the above embodiment, the case where the intraocular distance is obtained by using the measurement result obtained by the OCT measurement has been described, but the configuration of the ophthalmic apparatus according to the embodiment is not limited to this. The ophthalmic apparatus according to the embodiment can be applied to those that measure the intraocular distance by an ultrasonic method.

1 Z alignment system 2 XY alignment system 3 kerato measurement system 4 fixative 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 223 data processing Unit 231 Intraocular distance calculation unit 232 Judgment unit 233 Myopia progression estimation unit 233A Multivariate analysis unit 233B Progress information generation unit 1000 Ophthalmic device

Claims (21)

A refractive power measuring unit that acquires the measured value of the refractive power of the eye to be inspected,
An intraocular distance measuring unit that acquires a measured value of one or more intraocular distances in the eye to be inspected, and an intraocular distance measuring unit.
A storage unit that stores in advance standard data in which the information of the subject is associated with the refractive power of the eye of the subject who is a normal eye and the intraocular distance of 1 or more.
The measured value of the refractive power acquired by the refractive power measuring unit, the measured value of the intraocular distance of 1 or more acquired by the intraocular distance measuring unit, the information of the subject, and the standard data. An analysis unit that determines whether or not the eye to be inspected has axial myopia based on
Including
The analysis unit refers to the first analysis information obtained in advance based on the standard data with at least one of the refractive power of the eye, the distance within the eye of 1 or more, and the information of the person to be measured as variables. By doing so, the progress information of the axial myopia is generated.
The progress information includes an estimated value of the refractive power and the refractive power after the measurement timing of at least one of the above-mentioned intraocular distances and at least one of the above-mentioned intraocular distances. The analysis unit compares the measured value of the refractive power, the measured value of the intraocular distance of 1 or more, the information of the subject, and the standard data to determine whether the eye to be inspected has axial myopia. The ophthalmic apparatus according to claim 1, wherein it is determined whether or not the device is used. Claim 1 or claim 2 comprises a control unit that causes a display means to display information corresponding to a determination result indicating whether or not the eye to be inspected is axial myopia obtained by the analysis unit. The described ophthalmic device. A refractive power measuring unit that acquires the measured value of the refractive power of the eye to be inspected,
An intraocular distance measuring unit that acquires a measured value of one or more intraocular distances in the eye to be inspected, and an intraocular distance measuring unit.
A storage unit that stores in advance standard data in which the information of the subject is associated with the refractive power of the eye of the subject who is a normal eye and the intraocular distance of 1 or more.
The measured value of the refractive power acquired by the refractive power measuring unit, the measured value of the intraocular distance of 1 or more acquired by the intraocular distance measuring unit, the information of the subject, and the standard data. An analysis unit that generates information on the progress of axial myopia of the eye to be inspected based on
Including
The progress information includes an estimated value of the refractive power and the refractive power after the measurement timing of at least one of the above-mentioned intraocular distances and at least one of the above-mentioned intraocular distances . The analysis unit has two or more measurement values of the refractive force acquired by the refractive force measurement unit at different measurement timings, and two or more said 1s acquired by the intraocular distance measurement unit at different measurement timings. Claims 1 to 4 are characterized in that information on the progression of axial myopia of the subject's eye is generated based on the above measured values of the intraocular distance, the information of the subject, and the standard data. The ophthalmic apparatus according to any one of the above. A refractive power measuring unit that acquires the measured value of the refractive power of the eye to be inspected,
An intraocular distance measuring unit that acquires a measured value of one or more intraocular distances in the eye to be inspected, and an intraocular distance measuring unit.
A storage unit that stores in advance standard data in which the information of the subject is associated with the refractive power of the eye of the subject who is a normal eye and the intraocular distance of 1 or more.
Two or more measurement values of the refractive force acquired by the refractive force measuring unit at different measurement timings and two or more intraocular distances acquired by the intraocular distance measuring unit at different measurement timings. An analysis unit that generates information on the progress of axial myopia of the subject's eye based on the measured values of the subject, the information of the subject, and the standard data.
Including
The progress information includes an estimated value of the refractive power and the refractive power after the measurement timing of at least one of the above-mentioned intraocular distances and at least one of the above-mentioned intraocular distances . Based on the standard data, the analysis unit has at least information on the refractive power of the eye and the change in the refractive power, the change in the intraocular distance of 1 or more and the intraocular distance of 1 or more, and the information of the person to be measured. The ophthalmic apparatus according to claim 5 or 6 , wherein the progress information of the axial myopia is generated by referring to the second analysis information obtained in advance with one as a variable. The ophthalmology according to any one of claims 1 to 2 and 4 to 7 , wherein the ophthalmology includes a control unit for displaying the progress information obtained by the analysis unit on a display means. Device. The ophthalmic apparatus according to any one of claims 1 to 8 , wherein the information of the subject and the information of the subject include age and gender. The ophthalmic apparatus according to any one of claims 1 to 9 , wherein the information of the subject includes eye characteristic information of a close relative of the subject. The ophthalmic apparatus according to any one of claims 1 to 10 , wherein the one or more intraocular distance includes an axial length and a choroidal film thickness. The choroid thickness is at least one of the choroid thickness in the fovea, the average choroid near the fovea, the average choroid in each of the plurality of quadrants obtained by dividing the vicinity of the fovea, and the choroid around the macula. The ophthalmic apparatus according to claim 11 , wherein the ophthalmic apparatus comprises. The intraocular distance measuring unit is
OCT optics that divides the light from the light source into reference light and measurement light, projects the measurement light onto the eye to be inspected, and detects the interference light between the return light of the measurement light from the eye to be inspected and the reference light. System and
An intraocular distance calculation unit for obtaining an intraocular distance of 1 or more based on the detection result of the interference light obtained by the OCT optical system, and an intraocular distance calculation unit.
The ophthalmic apparatus according to any one of claims 1 to 12 , wherein the ophthalmic apparatus comprises. An acquisition step for acquiring the measured value of the refractive power of the subject, the measured value of one or more intraocular distances in the subject, and the information of the subject.
The measured value of the refractive force acquired in the acquisition step, the measured value of the intraocular distance of 1 or more, the information of the subject, the refractive force of the eye of the subject who is a normal eye, and the above 1. An analysis step for generating progressive myopia progression information for the eye under test based on standard data in which the information of the subject is associated with the above intraocular distance.
Let the computer run
The progress information is an ophthalmic information processing program including an estimated value of at least one of the refractive power and the refractive power of one or more intraocular distances after the measurement timing of at least one of the refractive power and the intraocular distance of one or more . In the analysis step, two or more measured values of the refractive power acquired in the acquisition step at different measurement timings, two or more measured values of the one or more intraocular distance, information on the subject, and the information of the subject. The ophthalmologic information processing program according to claim 14 , wherein information on the progression of axial myopia of the eye to be inspected is generated based on the standard data. An acquisition step for acquiring the measured value of the refractive power of the subject, the measured value of one or more intraocular distances in the subject, and the information of the subject.
Two or more measurement values of the refractive force acquired in the acquisition step at different measurement timings, two or more measurement values of the intraocular distance of one or more, information on the subject, and a normal eye subject. An analysis step to generate progress information of axial myopia of the eye to be inspected based on standard data in which the information of the person to be measured is associated with the refractive force of the eye of the measurer and the intraocular distance of one or more.
Let the computer run
The progress information is an ophthalmic information processing program including an estimated value of at least one of the refractive power and the refractive power of one or more intraocular distances after the measurement timing of at least one of the refractive power and the intraocular distance of one or more . The ophthalmic information processing program according to any one of claims 14 to 16 , further comprising a control step for displaying the progress information obtained in the analysis step on a display means. The ophthalmic information processing program according to any one of claims 14 to 17 , wherein the information of the subject and the information of the subject include age and gender. The ophthalmic information processing program according to any one of claims 14 to 18 , wherein the information of the subject includes eye characteristic information of a close relative of the subject. The ophthalmic information processing program according to any one of claims 14 to 19 , wherein the intraocular distance of 1 or more includes an axial length and a choroid film thickness. The choroid thickness is at least one of the choroid thickness in the fovea, the average choroid near the fovea, the average choroid in each of the plurality of quadrants obtained by dividing the vicinity of the fovea, and the choroid around the macula. The ophthalmic information processing program according to claim 20 , wherein the ophthalmic information processing program comprises.

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