JP6513747B2 - Ophthalmic device - Google Patents

Description

  The present invention relates to an ophthalmologic apparatus.

  Cataract is an eye disease in which visual acuity gradually decreases due to clouding of the lens serving as a lens. In general, cataract surgery is performed on an eye to which a cataract has progressed. For example, in cataract surgery, removing the turbid lens and inserting an intraocular lens (hereinafter referred to as an IOL) is performed instead. The IOLs include those having only sphericity, toric IOLs capable of correcting astigmatism, and multifocal IOLs capable of focusing on both far and near. Prior to cataract surgery, it is necessary to measure eye information that represents the structure of the subject's eye, such as the axial length, with an ophthalmologic apparatus, and to determine the IOL power from the measured eye information.

  Such an ophthalmologic apparatus is disclosed, for example, in Patent Document 1. Patent Document 1 includes an optical system for measuring the axial length and an optical system for measuring the refractive power of the subject's eye, and can measure the axial length and the refractive power of the subject's eye. An ophthalmic device is disclosed.

Patent No. 4523338 gazette

  In the eye to be examined with cataract, the transmittance of the lens decreases due to turbidity, so the light for measurement irradiated to the eye to be examined is diffused, and a sufficient amount of light does not reach the fundus, or return light from the fundus is It can not be detected sufficiently. As a result, in the conventional ophthalmologic apparatus, even if light is irradiated to the eye to be examined in which cataract progressed, even measurement can not be performed, and it may not be possible to determine the IOL frequency.

  The present invention has been made to solve the above-mentioned problems, and it is an object of the present invention to provide an ophthalmologic apparatus capable of obtaining the IOL power even in an eye to which a cataract has progressed.

The ophthalmologic apparatus according to the embodiment includes a reflex measurement projection system, a reflex measurement light receiving system, and a processing unit. The reflex measurement projection system projects the light output from the reflex measurement light source onto the fundus of the eye as a measurement pattern light flux. The reflex measurement light receiving system receives return light of the measurement pattern luminous flux projected onto the fundus by the reflex measurement projection system. The processing unit analyzes the image based on the return light received by the reflex measurement light receiving system to obtain the refractive power of the eye to be examined. The reflex measurement light source is disposed at a position substantially optically conjugate with the fundus of the eye to be examined. The reflex measurement projection system includes a conical prism, a relay lens, and a stop in which a pattern portion is formed. The conical prism condenses the light output from the reflex measurement light source on the pattern portion of the diaphragm through the relay lens. The light which has passed through the pattern portion of the diaphragm becomes the measurement pattern light flux.

  According to the ophthalmologic apparatus of the present invention, it is possible to obtain the IOL power even for an eye to be examined in which cataract has progressed.

It is a schematic diagram showing an example of composition of an ophthalmology device concerning an embodiment. It is the schematic which shows the structural example of the optical system of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the structural example of the optical system of the ophthalmologic apparatus which concerns on embodiment. It is operation | movement explanatory drawing which shows the operation example of the optical system of the ophthalmologic apparatus which concerns on embodiment. It is operation | movement explanatory drawing which shows the operation example of the optical system of the ophthalmologic apparatus which concerns on embodiment. It is operation | movement explanatory drawing which shows the operation example of the optical system of the ophthalmologic apparatus which concerns on embodiment. It is operation | movement explanatory drawing which shows the operation example of the optical system of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the structural example of the control system of the ophthalmologic apparatus which concerns on embodiment. It is the schematic which shows the structural example of the control system of the ophthalmologic apparatus which concerns on embodiment. It is a flowchart which shows the operation example of the ophthalmologic apparatus which concerns on embodiment. It is a flowchart which shows the operation example of the ophthalmologic apparatus which concerns on embodiment. It is a flowchart which shows the operation example of the ophthalmologic apparatus which concerns on embodiment. It is a flowchart which shows the operation example of the ophthalmologic apparatus which concerns on embodiment. It is a flowchart which shows the operation example of the ophthalmologic apparatus which concerns on the modification of embodiment. It is operation | movement explanatory drawing of the ophthalmologic apparatus which concerns on the modification of embodiment. It is operation | movement explanatory drawing of the ophthalmologic apparatus which concerns on the modification of embodiment.

  The ophthalmologic apparatus according to the embodiment is an apparatus capable of performing objective measurement and subjective measurement in one unit. The objective measurement is to obtain information on the subject's eye mainly using a physical method without referring to the response from the subject. The objective measurement includes a measurement for measuring a value related to an eye to be examined and a photographing for acquiring an image of the eye to be examined. Such objective measurement includes, for example, objective refraction measurement, corneal shape measurement, intraocular pressure measurement, fundus photography, OCT measurement using an optical coherence tomography (hereinafter referred to as OCT) method, etc. . The subjective measurement is to obtain the result based on the response from the subject. The subjective measurement includes, for example, subjective refraction measurement such as distance test, near test, contrast test, glare test, and visual field test. In the subjective measurement, information (such as a visual target) is presented to a subject, and a result is obtained based on the subject's response to the information.

  In this embodiment, the case of using an OCT technique of Fourier domain type in OCT measurement will be described. In particular, the ophthalmologic apparatus according to the embodiment can perform OCT measurement using the method of spectral domain OCT. The OCT measurement may use a type other than the spectral domain, for example, a method of swept source OCT. Moreover, it is also possible to use the method of OCT of a time-domain type | mold in OCT measurement in embodiment.

  In addition, the ophthalmologic apparatus according to the embodiment can perform at least one of arbitrary subjective measurement and arbitrary objective measurement. Hereinafter, the ophthalmologic apparatus according to the embodiment can perform distance vision inspection, near vision inspection, etc. as subjective measurement, and can perform objective refraction measurement, corneal shape measurement, OCT measurement, etc. as objective measurement. Device. In the OCT measurement, acquisition of eye information that represents the structure of the subject's eye, such as axial length, corneal thickness, anterior chamber depth, and lens thickness, is performed. Hereinafter, in OCT measurement, the case where eye axis length is acquired as eyeball information is explained. The configuration of the ophthalmologic apparatus according to the embodiment is not limited to the configuration described below. For example, objective refraction measurement may be performed by another device, and the measurement result may be input to perform eye axial length measurement.

<Appearance configuration>
FIG. 1 shows an appearance configuration of the ophthalmologic apparatus according to the embodiment. The ophthalmologic apparatus 1000 includes a base 200, a gantry 300, a head unit 400, a face receiving unit 500, a joystick 800, and a display unit 10.

  The gantry 300 is movable back and forth and right and left with respect to the base 200. The head unit 400 is configured integrally with the gantry 300. The face support unit 500 is integrally configured with the base 200.

  The face holder 500 is provided with a jaw holder 600 and a forehead holder 700. The face receiving unit 500 fixes the face of a subject (not shown). The examiner performs an examination, for example, on the opposite side of the subject across the ophthalmologic apparatus 1000. The joystick 800 and the display unit 10 are arranged at the position on the examiner side. The joystick 800 is provided on the gantry 300. The display unit 10 is provided on the surface of the head unit 400 on the side of the examiner. The display unit 10 is, for example, a flat panel display such as a liquid crystal display. The display unit 10 has a touch panel display screen 10a.

  The head unit 400 is moved back and forth and right and left by tilting operation of the joystick 800. In addition, the head unit 400 is moved in the vertical direction by rotating the joystick 800 about its axis. By these operations, the position of the head unit 400 with respect to the face of the subject held by the face receiving unit 500 is changed. The movement in the left and right direction is performed, for example, to switch the examination target by the ophthalmologic apparatus 1000 from the left eye to the right eye or from the right eye to the left eye.

  An external device 900 is connected to the ophthalmologic apparatus 1000. The external device 900 may be any device, and the connection manner (such as communication manner) between the ophthalmologic device 1000 and the external device 900 may be arbitrary. The external device 900 includes, for example, an eyeglass lens measurement device for measuring the optical characteristics of the lens. The spectacle lens measurement device measures the power of the spectacle lens worn by the subject and the like, and inputs this measurement data to the ophthalmic device 1000. Also, the external device 900 may be any other ophthalmologic device. Further, the external device 900 may be a device (reader) having a function of reading information from a recording medium, or a device (writer) having a function of writing information on a recording medium.

  Another example of the external device 900 is a computer used in the medical institution. Such in-hospital computers include, for example, a hospital information system (HIS) server, a digital imaging and communication in medicine (DICOM) server, a doctor terminal, and the like. The external device 900 may include a computer used outside the medical institution. Such an out-of-hospital computer includes, for example, a mobile terminal, a personal terminal, a server or terminal on the maker side of the ophthalmologic apparatus 1000, a cloud server, and the like.

<Configuration of optical system>
The ophthalmologic apparatus 1000 has an optical system for examining an eye to be examined. A configuration example of this optical system will be described with reference to FIGS. The optical system is provided in the head unit 400. The optical system includes a Z alignment projection system 1, an XY alignment spot projection system 2, a ring projection system 3 for kerato measurement, a fixation and subjective measurement system 4, an observation system 5, a reflex measurement projection system 6, a reflex It includes a measurement light receiving system 7 and an axial length measuring system 8. The processing unit 9 executes various processes.

  The Z alignment projection system 1 and the XY alignment spot projection system 2 are optical systems for projecting light necessary for performing alignment (XYZ alignment) of the optical system with the eye E. The Z alignment projection system 1 has a function for performing alignment in the direction (front-rear direction) along the optical axis of the observation system 5. The XY alignment spot projection system 2 has a function of projecting a spot for performing alignment in the direction (vertical direction, horizontal direction) orthogonal to the optical axis of the observation system 5. The ring projection system 3 for kerat measurement has a function of projecting a ring light flux for measurement for measuring the shape of the cornea K of the eye to be examined E onto the eye to be examined E. The fixation and subjective measurement system 4 is an optical system for presenting a fixation target and a target for subjective measurement to the eye E to be examined. The observation system 5 is an optical system for observing the anterior segment of the eye E to be examined. The reflex measurement projection system 6 is an optical system for projecting a light flux for objectively measuring the eye refractive power onto the subject's eye. The reflex measurement light receiving system 7 is an optical system for receiving the fundus reflected light of the light projected onto the subject's eye by the reflex measurement projection system 6. The axial length measurement system 8 is an optical system for measuring the axial length of the subject eye E by OCT measurement. The axial length measurement system 8 has a function of projecting the measurement light output from the OCT light source onto the fundus oculi Ef and a function of detecting the return light of the measurement light.

(Observation system 5)
The observation system 5 includes an objective lens 51, dichroic mirrors 52 and 53, an aperture 54, a half mirror 55, relay lenses 56 and 57, an imaging lens 58, and an imaging device (CCD) 59. The observation system 5 may further include an illumination light source for illuminating the anterior segment of the eye E. The output of the imaging element 59 is input to the processing unit 9. The processing unit 9 causes the display unit 10 to display an anterior segment image E ′ based on the signal input from the imaging device 59.

  A kerato plate 31 is provided between the objective lens 51 and the eye to be examined E. The kerato plate 31 is used to project a ring-shaped light flux for measuring the corneal shape on the cornea K of the eye E.

(Z alignment projection system 1 and XY alignment spot projection system 2)
A Z alignment projection system 1 is provided around the kerato plate 31. As described above, the Z alignment projection system 1 is used for alignment of the observation system 5 in the front-rear direction of the optical axis. The Z alignment projection system 1 has a Z alignment light source 11. The light from the Z alignment light source 11 is projected onto the cornea K. The light projected onto the cornea K is reflected by the cornea K and projected onto the line sensor 13 via the imaging lens 12. When the position of the corneal apex moves in the front-rear direction with respect to the optical axis of the observation system 5, the position of the light beam projected on the line sensor 13 changes. By analyzing the change in position, the position of the corneal apex of the eye to be examined E with respect to the objective lens 51 can be measured, and alignment can be performed based on the measurement value.

  The XY alignment spot projection system 2 forms an optical path branched from the observation system 5 via the half mirror 55. As described above, the XY alignment spot projection system 2 is used for alignment in the vertical and horizontal directions. The XY alignment spot projection system 2 has an XY alignment light source 21. A part of the light output from the XY alignment light source 21 is reflected by the half mirror 55, passes through the diaphragm 54, passes through the dichroic mirrors 53 and 52, passes through the objective lens 51, and is projected onto the eye E Be done. The light projected onto the subject's eye E is reflected by the cornea K, passes through the objective lens 51, and is projected onto the imaging device 59 via the same optical path as the observation system 5.

  As shown in FIG. 2 and the like, on the display screen 10a, the alignment mark AL and the bright spot image Br reflected by the cornea K are displayed together with the anterior eye part image E '. When performing alignment manually, the user operates the joystick 800 to adjust the position of the head unit 400 while referring to the information displayed on the display screen 10a, for example. At this time, the processing unit 9 may calculate the amount of displacement in the vertical and horizontal directions based on the amount of displacement of the bright spot image Br reflected by the alignment mark AL and the cornea K, for example, and may display it on the display screen 10a. Further, based on the processing information from the Z alignment projection system 1, the amount of deviation in the optical axis direction may be displayed on the display screen 10a. The processing unit 9 can perform control to start measurement in response to completion of alignment.

  When the alignment is automatically performed, the electric mechanism is controlled to move the head unit 400 so that the above-described deviation amount is cancelled. The mechanism includes an actuator that generates a driving force, and a member that transmits the driving force to the head unit 400. The processing unit 9 can perform control to start measurement in response to completion of alignment.

(Fixation and subjective measurement system 4)
The fixation and subjective measurement system 4 includes a light source 41, a transmission target chart 42, a focusing lens 43, a variable cross cylinder (hereinafter VCC) lens 44, and a reflection mirror 45. The focusing lens 43 is configured to be movable along the optical axis of the fixation and subjective measurement system 4. The fixation and subjective measurement system 4 may further include dichroic mirrors 53 and 52 and an objective lens 51.

  The fixation and subjective measurement system 4 can project a visual target for visual acuity measurement on the fundus oculi Ef of the eye to be examined E.

  The light (visible light) output from the light source 41 is irradiated to the target chart 42. The visual target chart 42 displays a visual target for visual acuity measurement, a fixation target such as a landscape chart, and transmits light output from the light source 41. The target chart 42 may be configured to include a transmissive liquid crystal panel. In this case, a target for vision measurement or a fixation target is displayed on the liquid crystal panel. The light transmitted through the target chart 42 passes through the focusing lens 43 and the VCC lens 44, is reflected by the reflection mirror 45, and is reflected by the dichroic mirror 53. The light from the light source 41 reflected by the dichroic mirror 53 passes through the dichroic mirror 52, passes through the objective lens 51, and is projected onto the fundus oculi Ef of the eye E. As a result, the visual target for measuring the visual acuity or the fixation target displayed on the visual target chart 42 is presented to the eye E. In objective refraction measurement, alignment is performed while the subject is gazing at a landscape chart projected onto the fundus oculi Ef, and the eye refractive power is measured in the state of foggy vision.

(Reflex measurement projection system 6 and reflex measurement light receiving system 7)
The reflex measurement projection system 6 and the reflex measurement light receiving system 7 constitute a reflex measurement system. The reflex measurement projection system 6 has a function of projecting the light (infrared light) output from the reflex measurement light source 61 onto the fundus oculi Ef of the eye E as a ring-shaped measurement pattern luminous flux. The reflex measurement light receiving system 7 has a function of receiving return light of the measurement pattern luminous flux projected onto the eye E by the reflex measurement projection system 6.

  The reflex measurement projection system 6 includes a reflex measurement light source 61, a condenser lens 62, a reflection mirror 63, a conical prism 64A, a relay lens 64B, a ring diaphragm 64C, an apertured prism 65, a rotary prism 66, and a quick. And a return mirror 67. The reflex measurement projection system 6 may further include a dichroic mirror 52 and an objective lens 51. The reflex measurement light source 61 is configured to be movable along the optical axis of the reflex measurement projection system 6. The reflex measurement light source 61 is disposed at a position substantially optically conjugate with the fundus oculi Ef of the eye to be examined E. As a result, the light from the reflex measurement light source 61 passes through the turbid lens and easily reaches the fundus oculi Ef.

  The reflex measurement light receiving system 7 includes a relay lens 71, a focusing lens 72, an imaging lens 73, and an imaging device (CCD) 74. The reflex measurement light receiving system 7 may further include an objective lens 51, a dichroic mirror 52, a quick return mirror 67, a rotary prism 66, and a holed prism 65. The focusing lens 72 is configured to be movable along the optical axis of the reflex measurement light receiving system 7. The focusing lens 72, the reflex measurement light source 61, and the focusing lens 85 of the eye axis length measurement system 8, which will be described later, are moved in the respective optical axis directions in cooperation. The output of the imaging element 74 is input to the processing unit 9. The objective lens 51, the dichroic mirror 52, the quick return mirror 67, the rotary prism 66, and the apertured prism 65 are shared with the reflex measurement projection system 6.

  The light output from the reflex measurement light source 61 passes through the condenser lens 62, is reflected by the reflection mirror 63, passes through the conical prism 64A and the relay lens 64B, and is guided to the ring diaphragm 64C. The light guided to the ring diaphragm 64C passes through the ring-shaped pattern portion to form a ring-shaped measurement pattern luminous flux. The conical prism 64A condenses the light from the reflex measurement light source 61 condensed by the condenser lens 62 on the ring-shaped pattern portion of the ring diaphragm 64C. The measured pattern light beam is reflected by the reflecting surface of the perforated prism 65, passes through the rotary prism 66, and is guided to the quick return mirror 67. By using the rotary prism 66, it is possible to average the light quantity distribution of the measurement pattern light flux to the blood vessel or the diseased site in the fundus oculi Ef.

  The quick return mirror 67 is used to switch between objective refraction measurement and axial length measurement. When performing the objective refraction measurement, the reflection surface of the quick return mirror 67 is disposed on the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52. As a result, both the optical path of the reflex measurement projection system 6 and the optical path of the reflex measurement light receiving system 7 are coupled to the optical path of the observation system 5. When performing axial length measurement, the quick return mirror 67 is retracted from the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52. Thereby, the optical path of the axial length measurement system 8 is coupled to the optical path of the observation system 5.

  Here, the reflection surface of the quick return mirror 67 is disposed on the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52. The measurement pattern light beam which has passed through the rotary prism 66 from the perforated prism 65 and is guided to the quick return mirror 67 is reflected by the quick return mirror 67, is reflected by the dichroic mirror 52, passes through the objective lens 51, It is projected on the optometry E.

  The return light of the measurement pattern light beam projected onto the eye E to be examined passes through the objective lens 51, is reflected by the dichroic mirror 52 and the quick return mirror 67, passes through the rotary prism 66, and the central portion of the apertured prism 65 pass. The light passing through the central portion of the perforated prism 65 passes through the relay lens 71 and the focusing lens 72, and is imaged on the imaging surface of the imaging element 74 by the imaging lens 73.

(Eye axis length measurement system 8)
The axial length measurement system 8 includes an OCT unit 80, a collimator lens 84, a focusing lens 85, a relay lens 86, an XY scanner 87, and a pupil lens 88. The eye axis length measurement system 8 may further include a dichroic mirror 52 and an objective lens 51. The dichroic mirror 52 and the objective lens 51 are shared with the observation system 5.

  The XY scanner 87 deflects light one-dimensionally or two-dimensionally. By performing deflection control on the XY scanner 87, it is possible to change the incident position of the measurement light LS described later on the eye E to be examined. In the case of two-dimensionally deflecting light, it is possible to use, as the XY scanner 87, a first deflecting member that deflects in a first direction and a second deflecting member that deflects in a second direction. The first direction is a direction substantially orthogonal (crossed) to the second direction. Examples of deflection members used for the XY scanner 87 include galvano mirrors, polygon mirrors, rotating mirrors, and the like. Also, Dove Prism, Double Dove Prism, Rotation Prism, MEMS mirror scanner, etc. may be used. The XY scanner 87 is disposed at a substantially optically conjugate position with the fundus oculi Ef of the eye E to be examined.

  The OCT unit 80 includes an OCT light source 81, a fiber coupler 82, and an optical path length changing unit 90. The OCT unit 80 may further include a spectroscope 83. The focusing lens 85 is configured to be movable along the optical axis of the eye axis length measurement system 8.

  The light (infrared light) output from the OCT light source 81 is split by the fiber coupler 82 into the measurement light LS and the reference light LR. The measurement light LS is output from the OCT unit 80 and guided to a collimator lens 84 by an optical fiber. The reference light LR is guided to the optical path length changing unit 90 by an optical fiber. The optical path length changing unit 90 changes the optical path length of the reference light LR.

  Here, the quick return mirror 67 is retracted from the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52. The measurement light LS is collimated by the collimator lens 84, passes through the focusing lens 85 and the relay lens 86, is deflected by the XY scanner 87, passes through the pupil lens 88, and is guided to the dichroic mirror 52. The measurement light LS from the OCT unit 80 guided to the dichroic mirror 52 is reflected by the dichroic mirror 52, passes through the objective lens 51, and is projected onto the fundus oculi Ef of the eye to be examined E.

  The return light of the measurement light projected onto the fundus oculi Ef passes through the objective lens 51 and is guided to the OCT unit 80 along the same path as the measurement light. The OCT unit 80 causes interference between the reference light whose optical path length has been changed by the optical path length changing unit 90 by the fiber coupler 82 and the return light of the measurement light to generate interference light LC. The optical path length changing unit 90 includes a collimator lens 91, a beam splitter 92, a retina shutter 93, a retina reference mirror unit 94, a cornea shutter 95, and a cornea reference mirror unit 96. The retina reference mirror unit 94 includes an imaging lens 94A and a reference mirror 94B. The cornea reference mirror unit 96 includes an imaging lens 96A and a reference mirror 96B. The beam splitter 92 splits the reference light path from which the reference light LR divided by the fiber coupler 82 is led into a reference light path for retina measurement and a reference light path for cornea measurement. The interference light LC is guided to the spectroscope 83 by an optical fiber. In the spectroscope 83, spatially wavelength-separated light is projected onto the line sensor. The processing unit 9 can extract information in the depth direction by performing signal processing such as known FFT (Fast Fourier Transform: hereinafter) on the signal output from the line sensor.

  The respective units of the ophthalmologic apparatus 1000 are controlled by the processing unit 9. The processing unit 9 includes the Z alignment light source 11, the XY alignment light source 21, the kerato ring light source 32 of the kerato plate 31, the light source 41, the reflex measurement light source 61, the OCT light source 81, the target chart 42, and the focusing lenses 43, 72, 85. Control. The processing unit 9 further controls the VCC lens 44, the quick return mirror 67, the optical path length changing unit 90, the display unit 10, and the like.

(Corneal shape measurement function)
When performing kerat measurement, the processing unit 9 turns on the kerat light source 32. The reflected light flux by the cornea of the ring-shaped light flux for corneal shape measurement projected onto the cornea K is projected onto the image pickup element 59 by the observation system 5 together with the anterior segment image. The processing unit 9 performs predetermined arithmetic processing on the image acquired by the imaging device 59 to calculate a parameter representing the shape of the cornea.

(Reflex measurement function)
When performing reflex measurement (objective refraction measurement), the processing unit 9 turns on the reflex measurement light source 61. The light from the reflex measurement light source 61 is projected onto the subject eye E as a ring-shaped measurement pattern luminous flux as described above. When the eye to be examined E is orthoscopic (= 0 D (diopter), the position where the reflex measurement light source 61 and the fundus oculi Ef of the examined eye E are conjugate is the reference position of the reflex measurement light source 61 and the focusing lens 72 . In this state, the luminous flux projected onto the fundus oculi Ef is reflected by the fundus oculi Ef, and a ring image based on the return light from the fundus oculi Ef is formed on the imaging element 74. Further, the reflex measurement light source 61 and the focusing lens 72 are moved to a position where the reflex measurement light source 61 and the fundus oculi Ef are substantially conjugate based on the measured value (refractive value) calculated from the formed ring image. The processing unit 9 analyzes the image based on the return light from the fundus oculi Ef detected by the imaging device 74, and takes into consideration the movement amount of the reflex measurement light source 61 to obtain the spherical power S as the refractive power of the eye E to be examined. The power C and the astigmatic axis angle A are determined.

  The reflex measurement light source 61 outputs broadband low-coherence light such as SLD (Super Luminescent Diode), for example. The reflex measurement light source 61 is, for example, a low coherence light source whose center wavelength is in the range of 820 nm to 880 nm. This makes it possible to measure objective refraction while reducing the burden on the subject due to visual recognition of the measurement light.

(Axle length measurement function)
Axial length measurement is performed using an OCT measurement function. When performing eye axial length measurement, the processing unit 9 controls the optical path length changing unit 90 to measure the distance from the corneal apex of the eye E to be measured to the retina as the eye axial length. First, the processing unit 9 turns on the OCT light source 81. The optical path length changing unit 90 is controlled in synchronization with the lighting of the OCT light source 81. Specifically, the corneal shutter 95 is inserted into the optical path between the beam splitter 92 and the corneal reference mirror unit 96, and the retinal shutter 93 is from the optical path between the beam splitter 92 and the retina reference mirror unit 94. Be evacuated. The light L0 from the OCT light source 81 is split by the fiber coupler 82 into the measurement light LS and the reference light LR. The measurement light LS is projected onto the fundus oculi Ef of the eye E as described above. At this time, the quick return mirror 67 is retracted out of the optical path. Further, according to the refractive power measurement result of the subject eye E described above, the focusing lens 85 is moved so that the end face of the fiber 80a is conjugate to the fundus oculi Ef of the subject eye E. The light reflected by the fundus oculi Ef returns along the same optical path and is projected on the end face of the fiber and reaches the fiber coupler 82.

  On the other hand, the reference light LR is collimated by the collimator lens 91 and is split into two light beams (for the cornea and for the retina) by the 50:50 beam splitter 92. The light beam for the retina divided by the beam splitter 92 is focused on a reference mirror (reflection mirror) 94B by an imaging lens 94A. The light beam for the cornea divided by the beam splitter 92 is condensed on a reference mirror (reflection mirror) 96B by an imaging lens 96A. Here, as described above, since the cornea shutter 95 is inserted in the light path and the retina shutter 93 is retracted from the light path, only the light reflected from the reference mirror 94 B returns in the same path, and the fiber coupler 82 is returned. To reach. The light reflected by the fundus oculi Ef and the reference mirror 94B is combined by the fiber coupler 82 and guided to the spectroscope 83 as an interference signal (interference light LC). In the spectroscope 83, spatially wavelength-separated light is projected onto the line sensor. The processing unit 9 can extract information in the depth direction by performing signal processing such as known FFT on the signal output from the line sensor.

  The retina reference mirror unit 94 and the cornea reference mirror unit 96 are moved so that the position of the interference signal becomes a predetermined position in the depth direction in accordance with the axial length of the eye E to be examined. For example, the intensity change of the interference signal after FFT in the depth direction is represented as shown in FIG. In this case, by moving the reference mirror unit for retina 94 in the optical axis direction as shown in FIG. 4, the position of the interference signal SC0 by the retina is moved so as to be at a predetermined position within a predetermined range as shown in FIG. can do. Here, the position of the reference mirror 96B may be fixed.

  Furthermore, since the corneal apex coordinates are detected using the above-described Z alignment projection system 1, it is possible to always adjust the distance between the corneal apex and the objective lens 51 (working distance) within a certain distance. Here, when the corneal shutter 95 is retracted from the optical path, an interference signal with light reflected by the cornea K of the eye E among the light projected onto the eye E is simultaneously projected on the spectroscope 83. When the working distance is within the predetermined range, the reference mirror 96B is arranged at a distance d from the position of the cornea so as not to overlap with the interference signal SC1 by the retina (FIG. 6). Therefore, as shown in FIG. 7 (which represents the intensity change of the interference signal after FFT in the depth direction as in FIG. 5), two interference signals (the interference signal SC1 due to the retina and the interference signal SC1 by the retina) are simultaneously It is possible to obtain the corneal interference signal SC2). In particular, when the signal sensitivity SC changes as shown in FIG. 7, the interference signal SC1 due to the retina with a weak signal component is detected in the measurement range R1 with high signal sensitivity, and the interference signal SC2 due to the cornea with a strong signal component is detected as the signal sensitivity. Detect in the weak measurement range R2. Thereby, two interference signals can be acquired simultaneously with high accuracy.

  When the OCT unit 80 has the same configuration as that of the swept source type OCT apparatus, a wavelength swept light source is provided instead of the OCT light source 81 that outputs low coherence light, and an optical member for spectrally resolving interference light is provided. I can not. With respect to the configuration of the OCT unit 80, any known technique according to the type of OCT can be applied.

  The OCT light source 81 outputs broadband low coherence light L0 such as SLD, for example. The OCT light source 81 is, for example, a low coherence light source whose center wavelength is in the range of 820 nm to 880 nm or 1040 to 1060 nm. This makes it possible to perform OCT measurement while reducing the burden on the subject due to visual recognition of the measurement light.

  A glass block or a density filter may be disposed in the optical path of the reference light LR between the collimator lens 91 and the reference mirrors 94B and 96B. The glass block and the density filter function as delay means for adjusting the optical path lengths (optical distance) of the reference light LR and the measurement light LS. The glass block and the density filter function as means for matching the dispersion characteristics of the reference light LR and the measurement light LS or the dispersion characteristics of the retina reference mirror unit 94 and the cornea reference mirror unit 96.

  The spectroscope 83 includes, for example, a collimator lens, a diffraction grating, an imaging lens, and a CCD. The interference light LC incident on the spectroscope 83 is collimated by the collimator lens and then split (spectral resolution) by the diffraction grating. The dispersed interference light LC is imaged on the imaging surface of the CCD by the imaging lens. The CCD receives the interference light LC, converts it into an electrical detection signal, and outputs the detection signal to the processing unit 9. The processing unit 9 generates OCT information (for example, image data and the like) of the tomographic image of the eye E based on the detection signal from the CCD. This processing includes processing such as noise removal (noise reduction), filter processing, FFT, etc., as in the conventional spectral domain type OCT.

  In addition, when the OCT unit 80 has the same configuration as a swept source type OCT apparatus, the spectroscope 83 includes, for example, an optical splitter and a balanced photodiode (BPD). . The interference light LC incident on the spectroscope 83 is split by the light splitter and converted into a pair of interference lights. The BPD has a pair of photodetectors that respectively detect a pair of interference lights, and outputs the difference of detection signals (detection results) by these to the processing unit 9.

  Although a Michelson-type interferometer is adopted in this embodiment, an arbitrary type of interferometer such as a Mach-Zehnder-type can be adopted appropriately.

(Awareness measurement function)
When the subjective measurement is performed, the processing unit 9 controls the target chart 42 to display a desired target. Further, the processing unit 9 moves the focusing lens 43 to a position according to the result of objective measurement. Similarly, the processing unit 9 may control the VCC lens 44 so that the astigmatic state is corrected based on the astigmatic state (degree of astigmatic power, astigmatic axis angle) of the subject eye E obtained by objective measurement. It is possible. The astigmatic power can be changed by independently rotating the two cylinder lenses constituting the VCC lens 44 in opposite directions. The astigmatic axis angle can be changed by rotating the two cylinder lenses constituting the VCC lens 44 in the same direction by the same angle.

  When the examiner or the processing unit 9 selects a target, the processing unit 9 controls the target chart 42 to display a desired target. The light from the target is projected onto the fundus oculi Ef via the focusing lens 43, the VCC lens 44, the reflecting mirror 45, the dichroic mirrors 53 and 52, and the objective lens 51.

  The subject responds to the visual target projected onto the fundus oculi Ef. For example, in the case of a visual acuity measurement target, the subject's response determines the visual acuity value of the subject's eye. For example, in the case of an astigmatic examination, a dot chart is driven and displayed, and the astigmatic power of the subject's eye is determined by the response of the subject. Selection of a visual target and the subject's response thereto are repeatedly performed according to the judgment of the examiner or the processing unit 9. The examiner or processing unit 9 determines the visual acuity value or the prescribed value (S, C, A) based on the response from the subject.

  Configuration of fixation and subjective measurement system 4, configuration of Z alignment projection system 1 and XY alignment spot projection system 2, configuration of kerato system, measurement principle of eye refractive power (reflex), measurement principle of subjective measurement, measurement of corneal shape The principle and the like are known. Therefore, detailed description about these is omitted in this embodiment.

(Configuration of information processing system)
The information processing system of the ophthalmologic apparatus 1000 will be described. An example of the functional configuration of the information processing system of the ophthalmologic apparatus 1000 is shown in FIG. 8 and FIG. The information processing system includes a control unit 110, an arithmetic processing unit 120, a display unit 170, an operation unit 180, and a communication unit 190. The control unit 110 includes an arithmetic processing unit 120, a Z alignment projection system 1, an XY alignment spot projection system 2, a ring projection system 3 for kerat measurement, a fixation and subjective measurement system 4, an observation system 5, a reflex measurement projection system 6, a reflex The measurement light receiving system 7 and the axial length measuring system 8 are controlled. Further, the control unit 110 controls the display unit 170 and the communication unit 190. The control of the Z alignment projection system 1 includes control of the Z alignment light source 11 and control of the line sensor 13. As control for the XY alignment spot projection system 2, control for the XY alignment light source 21 or the like is given. As control with respect to the ring projection system 3 for kerat measurement, there is control with respect to the kerat light source 32 or the like. The processing unit 9 includes, for example, a control unit 110 and an arithmetic processing unit 120.

(Control unit 110)
The control unit 110 includes a main control unit 111 and a storage unit 112. The control unit 110 is configured to include, for example, a microprocessor, a random access memory (RAM), a read only memory (ROM), a hard disk drive, and the like.

(Main control unit 111)
The main control unit 111 performs various controls of the ophthalmologic apparatus 1000. The main control unit 111 controls the Z alignment light source 11 and the line sensor 13 of the Z alignment projection system 1, the XY alignment light source 21 of the XY alignment spot projection system 2, and the kerat light source 32 of the ring projection system 3 for kerat measurement. As a result, the light amount of the light output from the Z alignment light source 11, the XY alignment light source 21, or the kerato ring light source 32 is changed, or the lighting or non-lighting is switched. Further, a signal detected by the line sensor 13 is captured, and alignment control and the like based on the captured signal are performed.

  The main control unit 111 controls the light source 41 of the fixation and subjective measurement system 4, the target chart 42, the focusing lens 43, and the VCC lens 44. Thereby, the light amount of the light output from the light source 41 is changed, lighting or non-lighting is switched, a visual target or a fixation target is displayed on the visual target chart 42, the optical axis direction of the focusing lens 43 The position of is changed. In addition, the astigmatism state of the eye E is corrected by the VCC lens 44 or the like.

  The main control unit 111 controls the imaging device 59 of the observation system 5. Thereby, the signal acquired by the imaging element 59 is taken in, and the formation of an image or the like is performed by the arithmetic processing unit 120. When the observation system 5 is configured to include an illumination light source, the main control unit 111 can control the illumination light source.

  The main control unit 111 controls the reflex measurement light source 61, the rotary prism 66, and the quick return mirror 67 of the reflex measurement projection system 6. As a result, the reflex measurement light source 61 is moved along the optical axis of the reflex measurement projection system 6, the amount of light output from the reflex measurement light source 61 is changed, and lighting and non-lighting are switched. In addition, the rotary prism 66 is rotated, or the light path is switched by the quick return mirror 67.

  The main control unit 111 controls the focusing lens 72 and the imaging device 74 of the reflex measurement light receiving system 7. As a result, the position of the focusing lens 72 in the optical axis direction is changed, a signal acquired by the imaging device 74 is taken in, and the image processing is performed by the arithmetic processing unit 120.

  The main control unit 111 controls at least one of the light amount of light output from the reflex measurement light source 61, the detection sensitivity of the imaging device 74, the exposure time, and the number of superimposed images based on the light detected by the imaging device 74. It is possible to change. Thereby, the conditions of measurement using the reflex measurement projection system 6 and the reflex measurement light receiving system 7 are changed.

  The main control unit 111 includes an OCT light source 81 of the eye axis length measurement system 8, a spectroscope 83, a focusing lens 85, an XY scanner 87, a shutter 93 for retina, a shutter 95 for cornea, a reference mirror unit 94 for retina, and the cornea. The reference mirror unit 96 is controlled. As a result, the light amount of light output from the OCT light source 81 is changed, switching between lighting and non-lighting is performed, a signal acquired by the spectroscope 83 is taken in, and the processing of the image is performed by the processing unit 120. The position of the focusing lens 85 in the optical axis direction is changed. In addition, the incident position of the measurement light LS to the eye E to be examined is changed, or the position of the reference mirror is changed. The main control unit 111 may move the focusing lens 85 along the optical axis of the axial length measurement system 8 in conjunction with the reflex measurement light source 61 and the focusing lens 72. Further, the main control unit 111 may further move the focusing lens 43 along the optical axis in conjunction with the focusing lens 85.

  The main control unit 111 changes at least one of the light amount of light output from the OCT light source 81, the detection sensitivity of the spectroscope 83, the exposure time, and the number of superimposed images based on the light detected by the spectroscope 83. It is possible. As a result, the conditions of measurement using the axial length measurement system 8 are changed.

  Further, the main control unit 111 performs a process of writing data in the storage unit 112 and a process of reading data from the storage unit 112.

(Storage unit 112)
The storage unit 112 stores various data. The data stored in the storage unit 112 includes, for example, image data of OCT information, image data of a fundus image, eye information to be examined, and the like. The subject's eye information includes information on the subject such as patient ID and name, and information on the subject's eye such as identification information of the left eye / right eye. The measurement information is stored in the storage unit 112 when the eye refractive power measurement of the eye E is performed inside or outside the ophthalmologic apparatus 1000. The storage unit 112 also stores various programs and data for operating the ophthalmologic apparatus 1000.

(Display unit 170, operation unit 180)
The display unit 170 receives control of the control unit 110 and displays information. The display unit 170 includes the display unit 10 shown in FIG.

  The operation unit 180 is used to operate the ophthalmologic apparatus 1000. The operation unit 180 includes various hardware keys (a joystick 800, buttons, switches, etc.) provided in the ophthalmologic apparatus 1000. The operation unit 180 also includes various software keys (buttons, icons, menus, etc.) displayed on the touch panel display screen 10a.

  At least a part of the display unit 170 and the operation unit 180 may be integrally configured. As a typical example, there is a touch panel display screen 10a.

(Communication unit 190)
The communication unit 190 has a function for communicating with the external device 900 shown in FIG. Communication unit 190 may be provided, for example, in processing unit 9. Communication unit 190 has a configuration according to the form of communication with external device 900.

(Operation processing unit 120)
As shown in FIG. 9, the arithmetic processing unit 120 includes an eye refractive power calculation unit 121, an eye axial length calculation unit 122, and an IOL power calculation unit 123. The eye refractive power calculation unit 121 includes a first refractive power calculation unit 121A and a second refractive power calculation unit 121B. The arithmetic processing unit 120 also takes in the signals acquired by the line sensor 13, the imaging devices 59 and 74, and the spectroscope 83, and performs various controls, formation of an image, analysis, and the like.

  The eye refractive power calculation unit 121 calculates the refractive power of the eye to be examined E. The eye refractive power calculation unit 121 determines the refractive power of the eye to be examined E in refractive power measurement using the reflex measurement projection system 6 and the reflex measurement light receiving system 7, or in the refractive power measurement using the axial length measurement system 8. The refractive power of the optometry E is determined. The main control unit 111 executes the refractive power measurement of the eye E using the eye axis length measurement system 8 based on the measurement result of the refractive power measurement using the reflex measurement projection system 6 and the reflex measurement light receiving system 7 Is possible. When refractive power measurement is performed using the reflex measurement projection system 6 and the reflex measurement light receiving system 7, the refractive power of the eye to be examined E is determined by the first refractive power calculation unit 121A. When refractive power measurement is performed using the eye axial length measurement system 8, the refractive power of the eye to be examined E is determined by the second refractive power calculation unit 121B.

  The first refractive power calculation unit 121A analyzes the shape of the ring image based on the return light from the fundus oculi Ef of the ring-shaped measurement pattern light beam projected onto the eye to be examined E, and thereby the refractive power of the eyeball optical system of the eye to be examined E Calculate The first refractive power calculation unit 121A analyzes, for example, an image in which a ring image based on the return light is drawn, and obtains the barycentric position of the ring image. The first refractive power calculation unit 121A can obtain the position at the center of gravity of the ring image by obtaining the distribution of pixel values (brightness values) in the image. Next, the first refractive power calculation unit 121A scans pixel values (brightness values) in a plurality of scanning directions extending in the outer peripheral direction of the ring image centering on the determined barycentric position, and obtains luminance distribution in each scanning direction. . The first refractive power calculation unit 121A specifies a ring image by obtaining a center position within a predetermined brightness value range from the brightness distribution in each scanning direction, and performs an elliptical approximation process on the specified ring image The approximate ellipse is specified by. The first refractive power calculation unit 121A obtains the spherical dioptric power S, the astigmatic power C, and the astigmatic axis angle A according to a known equation using the major axis length and the minor axis length of the identified approximate ellipse. In addition, the first refractive power calculation unit 121A can obtain the deformation or displacement of the ring image obtained by the imaging element 74 from the reference pattern, and can obtain the refractive power of the eye E from the obtained deformation or displacement. is there.

  The second refractive power calculation unit 121B obtains at least the spherical diopter of the eye E by OCT measurement using the eye axis length measurement system 8. In this embodiment, the second refractive power calculator 121B can obtain the equivalent spherical power as the spherical power. The second refractive power calculation unit 121B searches for the peak value of the detection signal of the interference light LC by moving the reference mirror (for example, the reference mirror 94B) in OCT measurement, and specifies the peak position. The second refractive power calculation unit 121B obtains the equivalent spherical power based on the movement amount of the reference mirror from the reference position of 0 D and the deviation amount of the identified peak position from the reference position.

  In addition, the eye refractive power calculation unit 121 can calculate the corneal refractive power, the corneal astigmatism, and the corneal astigmatism axis angle by analyzing the keratling image acquired by the imaging device 59 of the observation system 5 . For example, the eye refractive power calculation unit 121 performs arithmetic processing on the acquired keratling image to calculate the corneal curvature radius of the strong principal meridian and weak principal meridian of the front of the cornea, and the corneal curvature radius calculated. Calculate corneal refractive power, corneal astigmatism and corneal astigmatism axis angle.

  The axial length calculation unit 122 calculates the axial length of the eye E using the two interference signals shown in FIG. 7 acquired using the axial length measurement system 8.

  The IOL power calculation unit 123 calculates the power of the IOL according to a known calculation formula using the eye refractive power and the axial length of the eye E to be examined. Note that the IOL power calculation unit 123 may obtain the power of the IOL using eye information other than the eye refractive power and the axial length. Such eyeball information includes corneal thickness, anterior chamber depth, lens thickness and the like.

  The reflex measurement projection system 6, the reflex measurement light receiving system 7, and the arithmetic processing unit 120 (first refractive power calculation unit 121A) are examples of the "first measurement unit" according to this embodiment. The reflex measurement projection system 6 and the reflex measurement light receiving system 7 are examples of the “measurement optical system” according to this embodiment. The imaging device 74 is an example of the “first detection unit” according to this embodiment. The axial length measurement system 8 and the arithmetic processing unit 120 (second refractive power calculation unit 121B) are examples of the “second measurement unit” according to this embodiment. The OCT unit 80 is an example of the “interference optical system” according to this embodiment. The spectroscope 83 is an example of the “second detection unit” according to this embodiment.

<Operation example>
An operation example of the ophthalmologic apparatus 1000 according to the embodiment will be described. In this embodiment, when the IOL power can not be determined using the measurement result obtained by objective refraction measurement for the eye E, at least the eye E is measured by OCT measurement using the axial length measurement system 8. Find the spherical power. In the following, as an example where the IOL power can not be determined, it is assumed that it is not possible to acquire a ring image based on the return light of the ring-shaped measurement pattern light beam projected onto the eye E to be examined. Although described, the embodiment is not limited thereto.

  10 to 12 show a flow chart of an operation example of the ophthalmologic apparatus 1000 according to this embodiment.

(S1)
First, after the face of the subject is fixed by the face receiving unit 500, in response to the operation of the examiner on the operation unit 180, the control unit 110 turns on the Z alignment light source 11, the XY alignment light source 21, and the light source 41. The processing unit 9 acquires an imaging signal of the anterior segment image formed on the imaging surface of the imaging element 59, and causes the display unit 170 (the display screen 10a of the display unit 10) to display the anterior segment image E ′. . Thereafter, the head unit 400 is moved to the examination position of the eye E. The examination position is a position at which the examination of the eye E can be performed. The eye to be examined E is disposed at the examination position via the above-mentioned alignment (alignment by the Z alignment projection system 1 and the XY alignment spot projection system 2 and the observation system 5). The movement of the head unit 400 is performed by the control unit 110 in accordance with an operation or instruction by the user or an instruction by the control unit 110. That is, movement of the head unit 400 to the examination position of the eye E to be examined and preparation for performing objective measurement are performed.

  Further, in the control unit 110, the reflex measurement light source 61, the focusing lens 72, the focusing lens 85, and the focusing lens 43 are interlocked and moved to the position of the origin, for example, 0D along the optical axis. The movement to the origin is performed by the control unit 110 in accordance with an operation or instruction by the user or an instruction by the control unit 110. When the operation or instruction for focus adjustment is finished by the user, or when it is determined by the control unit 110 that the focus adjustment is appropriate by a known method, the operation of the ophthalmologic apparatus 1000 shifts to S2.

(S2)
The control unit 110 arranges the reflection surface of the quick return mirror 67 on the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52. In S2, as described above, the ring-shaped measurement pattern luminous flux for reflex measurement is projected onto the eye E to be examined. A ring image based on the return light of the measurement pattern light beam from the eye to be examined E is imaged on the imaging surface of the imaging device 74.

(S3)
The control unit 110 determines whether or not a ring image based on the return light from the fundus oculi Ef detected by the imaging element 74 in S2 has been acquired. For example, the control unit 110 detects the position (pixel) of the edge of the image based on the return light detected by the imaging device 74, and the width of the image (the difference between the outer diameter and the inner diameter) is equal to or greater than a predetermined value By determining whether or not the ring can be formed based on a point (image) whose intensity is equal to or greater than a predetermined height, it is determined whether or not the ring image can be acquired. When it is determined that the ring image has been acquired (S3: Y), the operation of the ophthalmologic apparatus 1000 shifts to S4. When the ring image can not be acquired at the origin, for example, 0D, the reflex measurement light source 61, the focusing lens 72, the focusing lens 85, and the focusing lens 43 are interlocked to move to, for example, the + 10D and -10D positions. Make a decision on When it is determined that the ring image can not be acquired at any position (S3: N), the operation of the ophthalmologic apparatus 1000 shifts to S10.

(S4)
When it is determined that the ring image has been acquired (S3: Y), the control unit 110 executes the reflex measurement. In the reflex measurement, the first refractive power calculation unit 121A analyzes the ring image based on the measurement pattern light beam projected in S2 or the return light of the measurement pattern light beam newly projected in S4 as described above. Thereby, the spherical power S, the astigmatic power C, and the astigmatic axis angle A are obtained. The control unit 110 stores the calculated spherical power and the like in the storage unit 112. The operation of the ophthalmologic apparatus 1000 shifts to S5 in accordance with an instruction from the control unit 110 or an operation or instruction of the user on the operation unit 180.

(S5)
The control unit 110 turns on the kerat light source 32. When light is output from the kertling light source 32, a ring-shaped luminous flux for measuring the corneal shape is projected onto the cornea K. The eye refractive power calculation unit 121 calculates the corneal curvature radius by performing arithmetic processing on the image acquired by the imaging device 59, and the corneal refractive power, the corneal astigmatism, and the corneal astigmatism are calculated from the calculated cornea curvature radius. Calculate the axis angle. In the control unit 110, the calculated corneal refractive power and the like are stored in the storage unit 112. The operation of the ophthalmologic apparatus 1000 shifts to S6 in accordance with an instruction from the control unit 110 or a user operation or instruction on the operation unit 180.

(S6)
The control unit 110 retracts the quick return mirror 67 from the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52. Subsequently, the control unit 110 turns on the OCT light source 81 and executes the axial length measurement as described above. The axial length calculation unit 122 calculates the axial length. In the control unit 110, the calculated eye information is stored in the storage unit 112. When the axial length measurement is completed, the operation of the ophthalmologic apparatus 1000 shifts to S7. The transition to step S7 is performed by an instruction from the control unit 110 or by a user operation or instruction on the operation unit 180.

(S7)
For example, based on the user's instruction to the operation unit 180, the control unit 110 controls the target chart 42 to display a desired target. Further, the control unit 110 moves the focusing lens 43 to a position according to the result of objective measurement. The subject responds to the visual target projected onto the fundus oculi Ef. For example, in the case of a visual acuity measurement target, the subject's response determines the visual acuity value of the subject's eye. Selection of a visual target and a subject's response thereto are repeatedly performed according to the judgment of the examiner or the control unit 110. When the subjective measurement is finished, the operation of the ophthalmologic apparatus 1000 shifts to S8. The transition to S8 is performed by an instruction from the control unit 110 or by a user operation or instruction on the operation unit 180.

(S8)
The control unit 110 controls the VCC lens 44 so that the astigmatic state is corrected based on the astigmatic state (the astigmatic power and the astigmatic axis angle) of the subject eye E obtained by the objective measurement. The subject responds to the visual target projected onto the fundus oculi Ef. For example, in the case of a visual acuity measurement target, the subject's response determines the visual acuity value of the subject's eye. Selection of a visual target and a subject's response thereto are repeatedly performed according to the judgment of the examiner or the control unit 110. The examiner or control unit 110 determines the visual acuity value or the prescribed value (S, C, A) based on the response from the subject. When the correction is completed, the operation of the ophthalmologic apparatus 1000 proceeds to S9. The transition to S9 is performed by an instruction from the control unit 110 or by a user operation or instruction on the operation unit 180.

(S9)
The control unit 110 causes the IOL power calculation unit 123 to obtain the power of the IOL using the refractive power of the subject eye E obtained by the above-mentioned measurement and the axial length obtained at S6. The control unit 110 stores the obtained IOL frequency in the storage unit 112. Thus, the operation of the ophthalmologic apparatus 1000 ends (end).

(S10)
When it is determined that the ring image can not be acquired in S3 (S3: N), the control unit 100 retracts the quick return mirror 67 from the optical path branched from the optical path of the observation system 5 by the dichroic mirror 52, and the OCT light source 81 Turn on. At this time, the focusing lens 85 is disposed, for example, at the 0D position.

(S11)
The control unit 110 moves the reference mirror 94B of the retina reference mirror unit 94 along the optical axis, and detects the detection signal of the interference light LC generated by the return light of the measurement light LS from the fundus Ef of the eye E to be examined. A peak value equal to or higher than a predetermined peak value is searched.

(S12)
When it is determined that the peak value is detected by the search for the peak value (S12: Y), the operation of the ophthalmologic apparatus 1000 shifts to S13. If the peak value is not detected at the origin, for example, 0D, the reflex measurement light source 61, the focusing lens 72, the focusing lens 85, and the focusing lens 43 are interlocked to move to, for example, + 10D, -10D, Make a decision on When it is determined that the peak value is not detected by searching for the peak value at any position (S12: N), the operation of the ophthalmologic apparatus 1000 shifts to S19.

(S13)
When it is determined in S12 that a peak value is detected (S12: Y), the control unit 110 moves the focusing lens 85 so that a peak value having a higher peak value is detected. In conjunction with the focusing lens 85, the focusing lens 72 and the reflex measurement light source 61 are also moved along the optical axis of the reflex measurement light receiving system 7.

(S14)
The control unit 110 calculates an evaluation value indicating the degree of progression of the cataract from the new peak value obtained by the movement of the focusing lens 85 or the like in S13.

  For example, it is possible to divide in advance the degree of progression of cataract into multiple stages depending on the opacity of the lens. Evaluation values are assigned to each stage in advance. It is estimated that the opacity of the lens is reflected in the peak value obtained in S13. Therefore, the control unit 110 can obtain an evaluation value indicating the degree of progression of the cataract by specifying which of the plurality of stages the peak value obtained in S13 is.

(S15)
Next, the control unit 110 changes the reflex measurement condition. For example, as the first change control in S15, the control unit 110 controls the imaging element 74 to increase the detection sensitivity by the first change amount. The first change amount may be a predetermined amount, or may be determined based on the evaluation value obtained in S14. By raising the detection sensitivity, it becomes easy to detect the return light from the fundus oculi Ef of the eye to be examined E, and it becomes easy to acquire a ring image.

  In addition, as the second change control in S15, the control unit 110 controls the image pickup device 74 so that the exposure time becomes longer by the first change time, or superimposes an image based on light detected by the image pickup device 74. Control may be performed to increase the combined number by the first number of changes. For example, the first change time or the first change number may be a predetermined time or number, or may be determined based on the evaluation value obtained in S14. By increasing the exposure time or increasing the number of superimposed images, it becomes easy to detect the return light from the fundus oculi Ef of the eye to be examined E, and it becomes easy to acquire a ring image.

  Furthermore, the control unit 110 may control the reflex measurement light source 61 so as to increase the light amount of the light by the second change amount as the third change control in S15. For example, the second change amount may be a predetermined amount or may be determined based on the evaluation value obtained in S14. By increasing the light amount of the light source, the light amount reaching the fundus oculi Ef of the eye to be examined E can be increased, and the light amount of the return light can be increased.

  In S15, at least one of the first change control, the second change control, and the third change control is executed. Further, the control content to be executed among the first change control, the second change control, and the third change control may be determined based on the evaluation value obtained in S14. For example, the first change control, the second change control, and the third change control are alternatively selected based on the evaluation value. Also, for example, the control content of S15 may be determined in the order of priority of the first change control, the second change control, and the third change control.

(S16)
Next, as in S3, the control unit 110 determines whether a ring image based on the return light from the fundus oculi Ef can be acquired by the reflex measurement in which the measurement conditions are changed in S15. When it is determined that the ring image has been acquired (S16: Y), the operation of the ophthalmologic apparatus 1000 shifts to S4, and the reflex measurement is performed again. On the other hand, when it is determined that the ring image can not be acquired (S16: N), the operation of the ophthalmologic apparatus 1000 proceeds to S17.

(S17)
When it is determined that the ring image can not be acquired (S16: N), the control unit 110 determines whether or not to execute a retry. For example, the control unit 110 determines whether or not to execute the retry by determining whether or not the number of times the retry has been executed in S17 in the past is equal to or less than a predetermined number. When it is determined that the retry is to be performed (S17: Y), the operation of the ophthalmologic apparatus 1000 proceeds to S15. When it is determined that the retry is not to be performed (S17: N), the operation of the ophthalmologic apparatus 1000 proceeds to S18.

(S18)
When it is determined that the retry is not to be performed (S17: N), the control unit 110 obtains at least the spherical power in the second refractive power calculation unit 121B as described above. Details of S18 will be described later. The operation of the ophthalmologic apparatus 1000 shifts to S5.

(S19)
When it is determined in S12 that the peak value is not detected (S12: N), the control unit 110 changes the OCT measurement condition. For example, as the fourth change control in S19, the control unit 110 controls the spectroscope 83 to increase the detection sensitivity by the second change amount. The second change amount may be a predetermined amount, or may be determined based on the maximum value of the peak values searched in S11. By increasing the detection sensitivity, it becomes easy to detect the interference light based on the return light from the fundus oculi Ef of the eye to be examined E.

  Further, as the fifth change control in S19, the control unit 110 controls the spectroscope 83 so that the exposure time becomes longer by the second change time, or superimposes an image based on the light detected by the spectroscope 83. Control may be performed to increase the combined number by the second number of changes. For example, the second change time or the second change number may be a predetermined time or number, or may be determined based on the maximum value of peak values searched in S11. The interference light based on the return light from the fundus oculi Ef of the eye to be examined E can be easily detected by lengthening the exposure time or increasing the number of superimposed images.

  Furthermore, the control unit 110 may control the OCT light source 81 so as to increase the light amount of the light by the third change amount as the sixth change control in S19. For example, the third change amount may be a predetermined amount or may be determined based on the maximum value of the peak values searched in S11. By increasing the light amount of the light source, the light amount reaching the fundus oculi Ef of the eye to be examined E can be increased, and the light amount of interference light based on the return light can be increased.

  In S19, at least one of the fourth change control, the fifth change control, and the sixth change control is executed. Also, the control content to be executed among the fourth change control, the fifth change control, and the sixth change control may be determined based on the maximum value of the peak values searched in S11. For example, the fourth change control, the fifth change control, and the sixth change control are alternatively selected based on the maximum value of the searched peak values. Also, for example, the control content of S19 may be determined in the order of priority of the fourth change control, the fifth change control, and the sixth change control.

(S20)
Similar to S12, the controller 110 moves the reference mirror 94B of the retina reference mirror unit 94 along the optical axis, and generates interference light generated by the return light of the measurement light LS from the fundus Ef of the eye to be examined E A peak value equal to or higher than a predetermined peak value of a detection signal of LC is searched.

(S21)
When it is determined that the peak value is detected by the search for the peak value (S21: Y), the operation of the ophthalmologic apparatus 1000 shifts to S13. When it is determined that the peak value is not detected by the search for the peak value (S21: N), the operation of the ophthalmologic apparatus 1000 shifts to S22.

(S22)
When it is determined that the peak value is not detected (S21: N), the control unit 110 executes the retry by determining whether or not the number of times the retry has been performed in S22 is less than or equal to the predetermined number. It is determined whether or not. When it is determined that the retry is to be performed (S22: Y), the operation of the ophthalmologic apparatus 1000 proceeds to S19. When it is determined that the retry is not to be performed (S22: N), the operation of the ophthalmologic apparatus 1000 proceeds to S23.

(S23)
When it is determined that the retry is not to be performed (S22: N), the control unit 110 executes a measurement error process. The measurement error process includes a process of displaying on the display unit 170 that the measurement error is generated. The measurement error processing may include processing for displaying on the display unit 170 that acquisition of a highly reliable value is not possible by the measurement. Thus, the operation of the ophthalmologic apparatus 1000 ends (end).

  FIG. 13 shows a flowchart of a processing example of the calculation processing of the spherical power in S18 of FIG.

(S31)
When the operation of the ophthalmologic apparatus 1000 proceeds to S18, the control unit 110 acquires a peak value equal to or higher than a predetermined wave height value among peak values of the detection signal of the interference light LC searched in S11. In addition, when the peak value more than a predetermined wave height value can not be acquired, you may make it acquire the maximum value of the searched peak value.

(S32)
The control unit 110 obtains an equivalent spherical power as the spherical power in the second refractive power calculation unit 121B. The second refractive power calculation unit 121B specifies the position of the focusing mirror 85 at which the peak value is maximum in S31, and obtains the equivalent spherical power based on the movement amount of the focusing mirror 85 from the reference position of 0D. Above, control part 110 ends processing of calculation processing of spherical power (end).

  S10 to S22 and S31 to S32 are examples of the “new measurement” according to the embodiment. S13 to S17 are examples of the “first measurement control” according to the embodiment.

[effect]
The effects of the ophthalmologic apparatus 1000 according to the embodiment will be described.

  The ophthalmologic apparatus (for example, the ophthalmologic apparatus 1000) according to the embodiment includes a first measurement unit (for example, the reflex measurement projection system 6, the reflex measurement light receiving system 7, the first refractive power calculation unit 121A) and a second measurement unit (for example, , An eye axial length measurement system 8, a second refractive power calculation unit 121B, and a control unit (for example, control unit 110). The first measurement unit irradiates light from the first light source (for example, reflex measurement light source 61) to the eye to be examined (for example, the eye to be examined E), and detects the return light to measure the refractive power of the eye to be examined . The second measurement unit divides the light from the second light source (for example, the OCT light source 81) into the reference light (for example, the reference light LR) and the measurement light (for example, the measurement light LS), and At least the spherical power of the subject's eye is determined by irradiating and detecting interference light (for example, interference light LC) between the return light of the measurement light and the reference light. The control unit causes the second measurement unit to perform a new measurement based on the measurement result by the first measurement unit.

  According to such a configuration, even when the first measurement unit can not measure the refractive power of the eye E, at least the spherical power can be obtained using the second measurement unit. Thereby, it is possible to determine the IOL frequency even if cataract has progressed.

  The first measurement unit projects the measurement pattern onto the subject's eye and measures the refractive power by analyzing the shape of the pattern image based on the return light from the subject's eye, and the control unit analyzes the shape of the pattern image A new measurement may be performed by the second measurement unit based on the result.

  According to such a configuration, it is possible to determine whether or not the measurement by the first measurement unit can be performed by analyzing the pattern image based on the return light of the measurement pattern. Thus, even when the refractive power of the eye E can not be measured using a pattern image based on the return light of the measurement pattern, at least the spherical power can be obtained. Thereby, it is possible to determine the IOL frequency even if cataract has progressed.

  In addition, the control unit analyzes the shape of the pattern image obtained by changing the measurement conditions of the first measurement unit and re-executing the measurement of the refractive power before making the second measurement unit execute a new measurement. The first measurement control may be executed, and re-measurement by the first measurement unit or new measurement by the second measurement unit may be performed according to the analysis result of the shape of the pattern image in the first measurement control.

  According to such a configuration, it is determined whether the measurement by the first measurement unit is possible while changing the measurement conditions of the first measurement unit, and when it is determined that the measurement is possible, remeasurement by the first measurement unit is performed. As it is made to carry out, it is possible to obtain as accurate measurement value as possible using the first measurement unit.

  In addition, the control unit detects the peak position of the return light of the measurement light before making the second measurement unit perform a new measurement, and executes the first measurement control when the peak position is detected, and the peak is detected. When a position is not detected, the first measurement control is executed when a new return light peak position obtained by changing the measurement condition of the second measurement unit and re-executing at least the measurement of spherical power is detected. You may do it.

  According to such a configuration, it is determined whether measurement by the second measurement unit is possible while changing the measurement conditions of the second measurement unit, and when it is determined that the measurement is possible, re-measurement by the second measurement unit is performed. Since it is made to carry out, it is possible to obtain a measurement value as accurate as possible using the second measurement unit.

  In addition, the first measurement unit includes a measurement optical system (for example, the reflex measurement projection system 6 and the reflex measurement light receiving system 7), a first detection unit (for example, the imaging device 74), and a first refractive power calculation unit (for example, The first refractive power calculation unit 121A) may be included. The measurement optical system irradiates the subject's eye with light from the first light source and guides return light from the subject's eye. The first detection unit detects the return light guided by the measurement optical system. The first refractive power calculation unit determines the refractive power of the subject's eye based on the detection result of the return light obtained by the first detection unit. The control unit controls the amount of light from the first light source, the detection sensitivity of the return light by the first detection unit, the exposure time of the return light in the first detection unit, and the image based on the return light detected by the first detection unit. The measurement conditions of the first measurement unit are changed by changing at least one of the numbers of sheets to be superimposed.

  According to such a configuration, since the measurement condition of the first measurement unit is changed by controlling the first light source, the first detection unit, and the like, when the cataract progresses, the IOL frequency can be simply controlled. Can be determined.

  In addition, the second measurement unit includes an interference optical system (for example, an OCT unit 80), a second detection unit (for example, a spectroscope 83), and a second refractive power calculation unit (for example, a second refractive power calculation unit 121B). And may be included. The interference optical system divides the light from the second light source into reference light and measurement light, irradiates the measurement light to the eye to be examined, and generates interference light of the return light and the reference light. The second detection unit detects interference light. The second refractive power calculation unit obtains at least a spherical power based on the detection result of the interference light obtained by the second detection unit. The control unit controls the amount of light from the second light source, the detection sensitivity of the interference light by the second detection unit, the exposure time of the interference light in the second detection unit, and the image based on the interference light detected by the second detection unit. The measurement conditions of the second measurement unit are changed by changing at least one of the numbers of sheets to be superimposed.

  According to such a configuration, since the measurement condition of the second measurement unit is changed by controlling the second light source, the second detection unit, and the like, when the cataract progresses, the IOL frequency can be simply controlled. Can be determined.

  The measurement pattern may be a ring-shaped pattern.

  According to such a configuration, since the refractive power of the eye to be examined is measured using the measurement pattern on the ring by the first measurement unit, a case where cataract progresses while using a general reflex measurement Even if there is, IOL frequency can be determined.

  In addition, the second measurement unit may include an eye axial length calculation unit (for example, an eye axial length calculation unit 122). The axial length calculation unit determines the axial length of the subject's eye by detecting the interference light.

  According to such a configuration, when it is not possible to measure the refractive power of the subject eye E by the first measurement unit, at least the spherical power is used while diverting the measurement system of axial length used for calculating the power of the IOL. Since the determination is made, it is possible to miniaturize the device for determining the IOL frequency.

<Modification>
Although the above-mentioned embodiment explained the case where the 2nd refractive power calculation part 121B asked only spherical power (equivalent spherical power) using eye axis length measuring system 8, the composition of the ophthalmology device concerning an embodiment is this. It is not limited. The second refractive power calculation unit according to the modification of the embodiment determines the spherical dioptric power, the astigmatic power and the astigmatic axis angle using the eye axial length measurement system.

  The configuration and operation of the ophthalmologic apparatus according to the modification of the embodiment are substantially the same as the configuration and operation of the ophthalmologic apparatus according to the embodiment. In the following, the same parts as those in the above-described embodiment are denoted by the same reference numerals, and the present modification will be described focusing on differences from the embodiment.

  The ophthalmologic apparatus according to the present modification can obtain the spherical dioptric power, the astigmatic dioptric power, and the astigmatic axis angle by using the eye axis length measurement system as described below in S18 of FIG. 12.

  FIG. 14 is a flowchart of a process example of S18 of FIG. 12 according to the present modification. FIGS. 15 and 16 illustrate operation explanatory diagrams of S43 and S44 of FIG.

(S41)
In the present modification, when the operation of the ophthalmologic apparatus shifts to S18, the control unit 110 acquires a peak value equal to or higher than a predetermined peak value among peak values of the detection signal of the interference light LC searched in S11. In addition, when the peak value more than a predetermined wave height value can not be acquired, you may make it acquire the maximum value of a peak value.

(S42)
The control unit 110 circularly scans the pupil of the subject eye E with the measurement light LS by deflecting the measurement light LS with the XY scanner 87 (for example, on a circumference of 3 mm in diameter). For example, as shown in FIG. 15, scanning is performed at scan positions P1 to P8.

(S43)
The second refractive power calculation unit 121B moves the focusing lens 85 to a position where the peak value is maximum at each scan position of the scan positions P1 to P8, and obtains the spherical power from the position. In S43, the spherical power (equivalent spherical power) is obtained at each scan position, as in, for example, S31 to S32.

(S44)
The second refractive power calculation unit 121B obtains the spherical power, the astigmatic power, and the astigmatic axis angle (reflex value) from the distribution of the spherical power at each scan position obtained in S43.

  At each scan position, the position of the focusing lens 85 described above, that is, the spherical power is shifted by astigmatic power. The second refractive power calculation unit 121B may obtain the spherical power S, the astigmatic power C, and the astigmatic axial angle A of the eye E by analyzing the spherical power acquired at each of the scanning positions P1 to P8. It is possible. For example, the second refractive power calculation unit 121B obtains the average value of the spherical power at each scan position obtained in S43, and obtains the obtained average value for each position from the optical axis center position (center of gravity position) C1. Correspond to the distance (radius of the circular scan). The second refractive power calculation unit 121B obtains the difference between the spherical power at each scan position and the average value. The second refractive power calculation unit 121B identifies new positions P1 ′ to P8 ′ in consideration of the difference at each scan position with reference to the center position C1, and performs elliptical approximation processing on the identified new positions. By doing this, the approximate ellipse AE is identified (FIG. 16). The second refractive power calculation unit 121B calculates the spherical power S, the astigmatic power C, and the astigmatic axis angle A according to a known equation using the lengths of the major axis DL and the minor axis DS of the identified approximate ellipse AE. Ask.

  Above, the control part 110 complete | finishes the process of S18 of FIG. 12 which concerns on this modification (end).

  According to such a configuration, even if the refracting power of the subject eye E can not be measured by the reflex measurement, the spherical power S, the astigmatic power C, and the astigmatic axis angle A using the eye axis length measurement system You can ask for As a result, even if cataract has progressed, it is possible to determine the IOL frequency with higher accuracy than in the past.

(Other modifications)
The embodiment shown above or its modification is only an example for implementing this invention. A person who intends to practice the present invention can make any modification, omission, addition, and the like within the scope of the present invention.

  In the above embodiment or the modification thereof, an example in which the eye axial length is determined using the eye axial length measurement system has been described, but the corneal thickness, the anterior chamber depth, and the thickness of the lens body are similarly obtained using the eye axial length measurement system. It is possible to ask.

  The present invention is not limited to the optical elements and their arrangements described in the above embodiment or the modification thereof. For example, a beam splitter may be provided instead of the half mirror in the above embodiment or the variation thereof.

  For the device having any function that can be used in the ophthalmological field, such as an intraocular pressure measurement function, a fundus imaging function, an anterior segment imaging function, an optical coherence tomography (OCT) function, and an ultrasound examination function, the above embodiments. It is possible to apply the invention concerning the modification or its modification. The tonometry function is realized by a tonometer or the like, the fundus imaging function is realized by a fundus camera, a scanning ophthalmoscope (SLO) or the like, and the anterior segment imaging function is realized by a slit lamp or the like. The OCT function is realized by an optical coherence tomography and the like, and the ultrasonic inspection function is realized by an ultrasonic diagnostic apparatus and the like. In addition, the present invention can be applied to a device (multifunction machine) having two or more of such functions.

  Further, in the system to which the above-described embodiment and the variation thereof can be applied, the above-described embodiment and the variation thereof can be alternatively applied by switching the operation mode.

DESCRIPTION OF SYMBOLS 1 Z alignment projection system 2 XY alignment spot projection system 3 Ring projection system 4 for kerat measurement 4 fixation and awareness measurement system 5 observation system 6 reflex measurement projection system 7 reflex measurement light reception system 8 eye axis length measurement system 9 processing parts 10, 170 Display unit 80 OCT unit 110 Control unit 111 Main control unit 112 Storage unit 120 Calculation processing unit 121 Eye refractive power calculation unit 121A First refractive power calculation unit 121B Second refractive power calculation unit 122 Eye axial length calculation unit 123 IOL power calculation unit 1000 ophthalmologic equipment

Claims (4)

A reflex measurement projection system that projects the light output from the reflex measurement light source as a measurement pattern light flux onto the fundus of the eye to be examined;
A reflex measurement light receiving system for receiving return light of the measurement pattern light beam projected onto the fundus by the reflex measurement projection system;
A processing unit that analyzes the image based on the return light received by the reflex measurement light receiving system to determine the refractive power of the subject's eye;
The reflex measurement light source is disposed at a position approximately optically conjugate to the fundus of the eye to be examined .
The reflex measurement projection system includes a conical prism, a relay lens, and a stop formed with a pattern portion.
The conical prism focuses the light output from the reflex measurement light source on the pattern portion of the diaphragm via the relay lens.
An ophthalmologic apparatus , wherein the light having passed through the pattern portion of the diaphragm becomes the measurement pattern light beam . The reflex measurement light source is movable along an optical axis of the reflex measurement projection system,
The ophthalmic apparatus according to claim 1, wherein the refractive measurement light source so that the refractive measurement light source is disposed in the fundus and optically substantially conjugate position is moved. The ophthalmologic apparatus according to claim 2 , wherein the reflex measurement light source is moved based on the measurement value calculated by the processing unit from the image based on the return light. The ophthalmologic apparatus according to any one of claims 1 to 3 , wherein the reflex measurement light source is a low coherence light source whose center wavelength is included in a range of 820 nm to 880 nm.

Images