JP7266375B2 - Ophthalmic device and method of operation thereof - Google Patents

Description

The present invention relates to an ophthalmologic apparatus for fixation of an eye to be examined and an operating method thereof.

In an ophthalmic examination using an ophthalmologic apparatus (including various actions for obtaining data of an eye to be examined, such as examination, measurement, and photography), fixation is performed to examine a desired portion of the eye to be examined (see Patent Document 1). ). Visual fixation is achieved by emitting fixation light toward the subject's eye and causing the subject's eye to gaze at this fixation light. As such fixation, internal fixation and peripheral fixation are well known (see Patent Document 2).

In internal fixation, fixation light of a fixation target (bright point image) displayed by a target display unit such as a dot matrix liquid crystal display or matrix light emitting diode is projected onto the subject's eye through an objective lens by an optical system. This is a fixation method. In this internal fixation, it is possible to freely set the emission position of the fixation light with respect to the subject's eye.

For example, when obtaining data on the macula of the fundus, the fixation light emitted from the display position corresponding to the macula in the target display unit is projected onto the subject's eye through the center of the objective lens by the optical system. . The macula is guided to the inspection (photographing) position by the subject's eye fixating (gazing) on this fixation light. In addition, when obtaining data on the fundus peripheral part of the eye fundus, the fixation light emitted from the display position corresponding to the fundus peripheral part in the target display unit is passed through the lens peripheral part of the objective lens by the optical system to the eye to be examined. projected to When the eye to be inspected fixes its eyes on this fixation light, the eye to be inspected is largely rotated, so that the periphery of the fundus is guided to the inspection position.

Peripheral fixation is performed using multiple fixation lights arranged around the objective lens. By selectively turning on these fixation lamps, the subject's eye can be largely rotated in a desired direction. As a result, the peripheral part of the fundus is guided to the examination position.

JP 2018-038687 A JP 2017-143919 A

By the way, as in the examination of the periphery of the fundus or the like, the subject's eye may fixate on the fixation light emitted from the lens periphery of the objective lens, or the fixation light emitted from the fixation lamp arranged around the objective lens may be used. When the subject's eye fixates the visual light, the subject's eye may lose sight of the fixation light because the visual fixation light does not exist in the central region of the visual field range of the subject. In this case, the examiner can confirm the fixation state of the eye to be examined (whether or not the eye to be examined catches the fixation light, and in which direction the line of sight of the eye to be examined is directed with respect to the fixation light, etc.). Difficult to distinguish. Therefore, it is difficult for the examiner to appropriately call attention to the examinee. As a result, fundus data acquisition is executed in a state where the subject's eye is not fixating on the fixation light, and there is a risk that data on a desired inspection target site may not be obtained.

SUMMARY OF THE INVENTION It is an object of the present invention to provide an ophthalmologic apparatus and a method of operating the same that can easily determine the fixation state of an eye to be examined.

An ophthalmologic apparatus for achieving the object of the present invention comprises a fixation light emitting section for emitting fixation light, a line-of-sight position detecting section for detecting the line-of-sight position of an eye to be examined with respect to the fixation light emitting section, and a fixation light emitting section. When the direction perpendicular to the emission direction of the fixation light emitted from the part is defined as the vertical direction, the detection result of the line-of-sight position detection part and the emission position of the fixation light emitted from the fixation light emission part and an information generating unit that generates relative position information indicating the vertical relative position of the line-of-sight position with respect to the emission position, based on .

According to this ophthalmologic apparatus, it is possible to easily determine the fixation state of the subject's eye based on the relative position information.

An ophthalmologic apparatus according to another aspect of the present invention includes an output unit that displays or audio-outputs the relative position information generated by the information generation unit. This makes it possible to easily determine the fixation state of the subject's eye.

In the ophthalmologic apparatus according to another aspect of the present invention, the output unit outputs information when the amount of deviation in the vertical direction of the line-of-sight position with respect to the emission position is greater than a predetermined threshold based on the relative position information generated by the information generation unit. , relative position information display or audio output is executed, and display or audio output of the relative position information is omitted when the deviation amount is equal to or less than the threshold value. As a result, relative position information is displayed or output as audio only when it is necessary to call attention to the examiner or the like.

In the ophthalmologic apparatus according to another aspect of the present invention, the information generation unit generates a first image that is a first image representing relative position information and is centered on the emission position, and the output unit generates the first image. indicate. This makes it possible to easily determine the fixation state of the subject's eye.

In an ophthalmologic apparatus according to another aspect of the present invention, an optical system that irradiates an eye to be inspected with illumination light through an objective lens having an optical axis parallel to an emission direction and receives the reflected light of the illumination light reflected by the eye to be inspected. and the information generating unit generates, as the relative position information, a second image that is centered on the optical axis and that indicates the vertical relative positions of the emission position and the line-of-sight position with respect to the optical axis. , the output unit displays the second image. As a result, it is possible to easily determine the fixation state of the subject's eye, and the emission position and line-of-sight position with respect to the optical axis.

In the ophthalmologic apparatus according to another aspect of the present invention, the fixation light emitting section selectively emits the fixation light from a plurality of emission positions and includes an operation section that receives an emission position designation operation, and the information generation section includes: , to generate relative position information corresponding to the emission position selected by the specifying operation on the operation unit. Accordingly, even when the fixation light is selectively emitted from a plurality of emission positions, the fixation state of the subject's eye can be easily determined for each emission position.

In the ophthalmologic apparatus according to another aspect of the present invention, the fixation light emitting part is displayed on the eye target display part that displays the fixation target and on the eye target display part through an objective lens having an optical axis parallel to the emission direction. and a projection optical system for projecting fixation light corresponding to the fixation target onto the subject's eye.

In an ophthalmologic apparatus according to another aspect of the present invention, an optical system that irradiates an eye to be inspected with illumination light through an objective lens having an optical axis parallel to an emission direction and receives the reflected light of the illumination light reflected by the eye to be inspected. and the fixation light output section comprises a plurality of fixation lights surrounding the objective lens.

A method of operating an ophthalmologic apparatus for achieving the object of the present invention is a method of operating an ophthalmologic apparatus having a fixation light emitting portion that emits fixation light, wherein the line-of-sight position detecting portion , and the information generation unit sets the direction perpendicular to the emission direction of the fixation light emitted from the fixation light emission unit as the vertical direction, the detection result of the sight line position detection unit, Based on the emission position of the fixation light emitted from the fixation light emitting portion, relative position information indicating the vertical relative position of the line-of-sight position with respect to the emission position is generated.

The present invention can easily determine the fixation state of the subject's eye.

1 is a front perspective view of an ophthalmologic apparatus viewed from the subject's side; FIG. FIG. 4 is a rear perspective view of the ophthalmologic apparatus seen from the examiner's side; It is a front view of a lens accommodating part. 1 is a schematic diagram showing an example of the configuration of an ophthalmologic apparatus; FIG. It is a functional block diagram of an arithmetic control unit. FIG. 4 is an explanatory diagram showing an example of the relationship between the inspection target site of the fundus and the display position of the fixation target within the display surface of the optotype display unit. It is a front enlarged view of a lens accommodating part. FIG. 10 is an explanatory diagram for explaining a sight line position detection method of a sight line position detection unit using a Purkinje image; FIG. 10 is an explanatory diagram for explaining a method of detecting the line-of-sight direction of an eye to be inspected based on a captured image of the eye to be inspected; FIG. 5 is an explanatory diagram for explaining generation of relative position information by an information generation unit; FIG. 4 is an explanatory diagram showing a first example of relative position information; FIG. 9 is an explanatory diagram showing a second example of relative position information; FIG. 10 is an explanatory diagram showing an example of a photographing screen and relative position information superimposed on the display device during alignment of the retinal camera unit; FIG. 10 is an explanatory diagram showing an example of a photographing screen and relative position information superimposed on the display device when adjusting the focus of the retinal camera unit; FIG. 10 is an explanatory diagram showing an example of a photographing screen and relative position information superimposed on the display device during auto-optimization of the ophthalmologic apparatus; 4 is a flowchart showing the flow of inspection processing of an eye to be examined by an ophthalmologic apparatus, particularly display processing of relative position information on a display device. 10 is a flow chart showing the flow of inspection processing of an eye to be inspected by an ophthalmologic apparatus according to another embodiment, particularly display processing of relative position information on a display device.

[Overall Configuration of Ophthalmic Device]
FIG. 1 is a front perspective view of the ophthalmologic apparatus 1 viewed from the subject side. FIG. 2 is a rear perspective view of the ophthalmologic apparatus 1 viewed from the examiner's side. As shown in FIGS. 1 and 2, the ophthalmologic apparatus 1 is a multi-function device that combines a fundus camera and an optical coherence tomography (OCT) to obtain a tomographic image. .

In addition, the X direction in the figure is the lateral direction with respect to the subject (interpupillary direction of the subject's eye E shown in FIG. 4), the Y direction is the vertical direction, and the Z direction is before approaching the subject. The fore-and-aft direction (also referred to as the working distance direction) parallel to the direction and the rearward direction away from the subject.

The ophthalmologic apparatus 1 includes a base 400 , a face receiving section 401 , a pedestal 402 and a measurement head 403 . The base 400 stores an arithmetic control unit 200 (see FIG. 4), etc., which will be described later.

The face receiving portion 401 is provided integrally with the base 400 at a position on the front side of the measuring head 403 in the Z direction. The face support section 401 has a chin support 401a and a forehead support 401b whose positions are adjustable in the Y direction, and supports the subject's face.

The mount 402 is provided on the base 400 and is movable with respect to the base 400 in the X direction and the Z direction (front, back, left, and right). An operation unit 210 and a measurement head 403 are provided on the mount 402 .

The operation unit 210 is provided on the pedestal 402 and at a position on the rear side (examiner side) of the measuring head 403 in the Z direction. The operation unit 210 is provided with operation buttons for performing various operations of the ophthalmologic apparatus 1 and an operation lever 210a.

The operation lever 210a is an operation member for moving the measurement head 403 in each of the XYZ directions. For example, when the operation lever 210a is tilted in the Z direction (front-rear direction) or the X direction (left-right direction), the measuring head 403 is moved in the Z direction or the X direction by an electric driving mechanism (not shown). Further, when the operation lever 210a is rotated around its longitudinal axis, the measuring head 403 is moved in the Y direction (vertical direction) by the above-described electric drive mechanism according to the direction of the rotation operation. A measurement button is provided on the top of the operation lever 210a for starting the measurement of the subject's eye E (see FIG. 4) by the ophthalmologic apparatus 1. FIG.

The measurement head 403 incorporates a fundus camera unit 2 and an OCT unit 100 shown in FIG. 4 which will be described later. In addition, the display device 3 is provided on the back surface of the measuring head 403 on the rear side (examiner side) in the Z direction, and the lens accommodating section is provided on the front surface on the front side (examinee side) in the Z direction. 403a is provided.

The display device 3 is, for example, a touch panel type liquid crystal display device. The display device 3 displays various photographing screens 220 (see FIG. 13, etc.) displayed during examination of the eye to be examined E, various photographing data of the eye to be examined E, input screens for various setting operations, and the like. .

FIG. 3 is a front view of the lens accommodating portion 403a. The lens housing part 403a houses an objective lens 22 that constitutes a part of the retinal camera unit 2 (see FIG. 4) and has an optical axis OA parallel to the Z direction. In addition, eight fixation lamps 95 (corresponding to the fixation light emitting portion of the present invention) are arranged at equal intervals along the circumferential direction of the objective lens 22 so as to surround the objective lens 22 in the lens housing portion 403a. ) is provided. Each fixation light 95 selectively emits a fixation light in the Z direction in accordance with an operation for designating a region to be inspected on the operation unit 210 . Note that the arrangement position and number of arrangement of each fixation light 95 may be changed as appropriate.

Two anterior eye cameras 300 of the retinal camera unit 2 (see FIG. 4) are provided in front of the measuring head 403 and in the vicinity of the lens accommodating portion 403a.

Returning to FIGS. 1 and 2 , the face receiving portion 401 is provided with an external fixation light 96 . The external fixation light 96 has a light source that emits fixation light, and the position of this light source and the emission direction of the fixation light can be arbitrarily adjusted. This external fixation light 96 is used for external fixation. External fixation is a fixation method that adjusts the orientation of the subject's eye E by guiding the line of sight of the fellow eye when internal fixation of the subject's eye E cannot be performed.

FIG. 4 is a schematic diagram showing an example of the configuration of the ophthalmologic apparatus 1. As shown in FIG. As shown in FIG. 4, the ophthalmologic apparatus 1 includes a fundus camera unit 2, an OCT unit 100, an arithmetic control unit 200, and the like. The retinal camera unit 2 is accommodated in the measurement head 403 and has an optical system substantially similar to that of a conventional retinal camera. The OCT unit 100 is housed within the measurement head 403 and has an optical system for acquiring an OCT image of the fundus oculi Ef. The arithmetic control unit 200 is housed in the base 400 (which may be inside the measurement head 403), and is an arithmetic processing device such as a personal computer that executes various kinds of arithmetic processing and control processing.

[Fundus camera unit]
The fundus camera unit 2 includes an illumination optical system 10 and a photographing optical system 30 as optical systems for acquiring a two-dimensional image (fundus image) representing the surface morphology of the fundus Ef of the eye E to be examined. The illumination optical system 10 and the imaging optical system 30 function as the optical system of the present invention.

The illumination optical system 10 illuminates the fundus oculi Ef with illumination light. The imaging optical system 30 guides the fundus reflected light of the illumination light reflected by the fundus Ef to CMOS (Complementary Metal Oxide Semiconductor) type or CCD (Charge Coupled Device) type image sensors 35 and 38 . Further, the imaging optical system 30 guides the signal light output from the OCT unit 100 to the fundus oculi Ef, and guides the signal light to the OCT unit 100 via the fundus oculi Ef.

The illumination optical system 10 includes an observation light source 11, a reflecting mirror 12, a condenser lens 13, a visible cut filter 14, an imaging light source 15, a mirror 16, relay lenses 17 and 18, an aperture 19, a relay lens 20, an aperture mirror 21, and a dichroic. A mirror 46, an objective lens 22, and the like are provided.

In addition to the objective lens 22, the dichroic mirror 46, and the perforated mirror 21, the imaging optical system 30 includes a dichroic mirror 55, a focusing lens 31, a mirror 32, a half mirror 39A, a target display section 39, and a dichroic mirror. 33, a condenser lens 34, an image sensor 35, a mirror 36, a condenser lens 37, an image sensor 38, and the like.

The observation light source 11 is, for example, a halogen lamp or an LED (Light Emitting Diode) light source, and emits observation illumination light. Observation illumination light emitted from the observation light source 11 is reflected by the reflecting mirror 12, passes through the condenser lens 13, passes through the visible cut filter 14, and becomes near-infrared light. Further, the observation illumination light is once converged near the photographing light source 15 , reflected by the mirror 16 , and passed through the relay lenses 17 and 18 , the diaphragm 19 and the relay lens 20 . The observation illumination light is reflected by the periphery of the perforated mirror 21 (area around the perforation), passes through the dichroic mirror 46, is refracted by the objective lens 22, and illuminates the fundus oculi Ef.

The fundus reflected light of the observation illumination light is refracted by the objective lens 22, passes through the dichroic mirror 46, passes through a hole formed in the central region of the perforated mirror 21, passes through the dichroic mirror 55, and reaches the focusing lens. 31 and reflected by mirror 32 . Further, this fundus reflected light passes through the half mirror 39A, is reflected by the dichroic mirror 33, and is imaged on the light receiving surface of the image sensor 35 by the condenser lens . The image sensor 35 captures (receives) the reflected light from the fundus and outputs an imaging signal. The display device 3 displays an observed image based on the imaging signal output from the image sensor 35 . In addition, when the focus of the imaging optical system 30 is adjusted to the anterior segment Ea of the eye E to be examined, the observed image of the anterior segment Ea is displayed on the display device 3, and the focus of the imaging optical system 30 is focused on the fundus oculi Ef. When adjusted, an observed image of the fundus oculi Ef is displayed on the display device 3 .

The imaging light source 15 is, for example, a xenon lamp or an LED light source, and emits imaging illumination light. The imaging illumination light emitted from the imaging light source 15 irradiates the fundus oculi Ef through the same path as the observation illumination light described above. The fundus reflected light of the imaging illumination light is guided to the dichroic mirror 33 through the same path as the fundus reflected light of the observation illumination light. An image is formed on the light receiving surface of 38 .

The image sensor 38 captures (receives) the reflected light from the fundus and outputs an image signal. The display device 3 displays a photographed image based on the imaging signal output from the image sensor 38 . The display device 3 that displays the observed image and the display device 3 that displays the captured image may be the same or different.

Various display devices such as a dot matrix liquid crystal display (LCD) and a matrix light emitting diode (LED) are used for the optotype display unit 39, for example. This target display unit 39 displays a fixation target. In addition, the visual target display unit 39 can arbitrarily set the display mode (shape, etc.) and the display position of the fixation target. Note that the optotype display unit 39 can display not only the fixation target but also an optotype for visual acuity measurement.

Part of the fixation light of the fixation target displayed on the target display unit 39 is reflected by the half mirror 39A, and then passes through the mirror 32, the focusing lens 31, the dichroic mirror 55, and the holes of the aperture mirror 21. , the dichroic mirror 46, and the objective lens 22, and is projected onto the eye E to be examined. As a result, the eye E to be examined can be presented with a fixation target, a visual acuity measurement target, and the like. The half mirror 39A to the objective lens 22 described above correspond to the projection optical system of the present invention. Therefore, in this embodiment, a portion of the imaging optical system 30 (from the target display section 39 to the objective lens 22) also functions as the fixation light emitting section of the present invention.

The retinal camera unit 2 includes an alignment optical system 50 and a focus optical system 60, like a conventional retinal camera. The alignment optical system 50 generates an alignment index for aligning the fundus camera unit 2 with the eye E to be examined. The focus optical system 60 generates a split index for focusing on the fundus oculi Ef.

The alignment optical system 50 includes an LED 51 , diaphragms 52 and 53 and a relay lens 54 in addition to the objective lens 22 , the dichroic mirror 46 , the perforated mirror 21 and the dichroic mirror 55 already described. In addition to the objective lens 22, the dichroic mirror 46, and the perforated mirror 21, the focus optical system 60 includes an LED 61, a relay lens 62, a split indicator plate 63, a two-hole diaphragm 64, a mirror 65, and a condenser lens. 66, and a reflecting bar 67.

The alignment light emitted from the LED 51 of the alignment optical system 50 passes through the apertures 52 and 53 and the relay lens 54, is reflected by the dichroic mirror 55, passes through the perforated mirror 21, and passes through the dichroic mirror 46. , is projected onto the cornea of the anterior segment Ea of the eye E to be examined by the objective lens 22 .

The cornea-reflected light of the alignment light passes through the objective lens 22, the dichroic mirror 46, and the holes of the perforated mirror 21, and after part of it passes through the dichroic mirror 55, it passes through the focusing lens 31, the mirror 32, and the half mirror. 39A, the dichroic mirror 33, and the condenser lens 34, and is incident on the light receiving surface of the image sensor 35. FIG.

The image sensor 35 captures (receives) the corneal reflected light of the alignment light and outputs an image signal. As a result, the alignment index is displayed on the display device 3 together with the observation image of the anterior segment Ea. Then, the user carries out alignment by performing operations similar to those of a conventional fundus camera. Alternatively, the arithmetic and control unit 200 may analyze the position of the alignment index and move the optical system to perform alignment (auto-alignment).

The reflecting surface of the reflecting bar 67 is set on the optical path of the illumination optical system 10 when focus adjustment is performed by the focusing optical system 60 . The focused light emitted from the LED 61 passes through the relay lens 62 and is split into two light beams by the split index plate 63. After passing through the two-hole diaphragm 64, the mirror 65, and the condenser lens 66, the light is reflected by the reflecting rod 67. An image is once formed on the surface and reflected toward the relay lens 20 by this reflecting surface. Further, the focus light passes through the relay lens 20, the perforated mirror 21, the dichroic mirror 46, and the objective lens 22 and is projected onto the fundus oculi Ef.

The fundus reflected light of the focus light passes through the same path as the cornea reflected light of the alignment light and is captured by the image sensor 35 . The image sensor 35 captures the fundus reflected light of the focus light and outputs an image signal. Thereby, the split index is displayed on the display device 3 along with the observation image. The arithmetic control unit 200, which will be described later, analyzes the position of the split index and moves the focusing lens 31 and the like to automatically perform focusing as in the conventional art. Alternatively, the user may manually adjust the focus while visually recognizing the split indicator.

The dichroic mirror 46 branches the optical path for OCT measurement from the optical path for fundus imaging. The dichroic mirror 46 reflects light in the wavelength band used for OCT measurement and transmits light for fundus imaging. The optical path for OCT measurement includes, in order from the OCT unit 100 side, a collimator lens unit 40, an optical path length changing section 41, a galvanometer scanner 42, a focusing lens 43, a mirror 44, and a relay lens 45. is provided.

The optical path length changing unit 41 is movable in the direction of the arrow shown in FIG. 1, and changes the optical path length of the optical path for OCT measurement. This change in the optical path length is used for correction of the optical path length according to the axial length of the eye E to be examined, adjustment of the interference state, and the like. The optical path length changer 41 includes, for example, a corner cube and a mechanism for moving it.

The galvanometer scanner 42 changes the traveling direction of the signal light passing through the optical path for OCT measurement. Thereby, the fundus oculi Ef can be scanned with the signal light. The galvanometer scanner 42 includes, for example, a galvanometer mirror for scanning signal light in the X direction, a galvanometer mirror for scanning in the Y direction, and a mechanism for independently driving these. Thereby, the signal light can be scanned in any direction on the XY plane.

Furthermore, the retinal camera unit 2 is equipped with a line-of-sight position detection optical system 70 . The line-of-sight position detection optical system 70 includes a mirror 71, an infrared LED 72, a pinhole 73, a condenser lens 74, a mirror 75, an imaging lens 76, a mirror 77, an image sensor 78, and a semiconductor position detector. and a PSD 79 that is an element (Position Sensitive Detector).

The mirror 71 is arranged between the already-described dichroic mirror 46 and the objective lens 22, and a dichroic mirror is used, for example. This mirror 71 transmits the previously described illumination light, observation illumination light, signal light, etc. (including the reflected light thereof). The mirror 71 reflects near-infrared light incident from a mirror 75 (to be described later) toward the objective lens 22 , and reflects reflected near-infrared light incident from the objective lens 22 toward the mirror 75 .

The infrared LED 72 emits near-infrared light toward the pinhole 73 . The pinhole 73 converts the near-infrared light incident from the infrared LED 72 into a point light source, and then emits the near-infrared light from this point light source toward the condenser lens 74 . The condenser lens 74 emits the near-infrared light incident from the pinhole 73 toward the mirror 75 .

A half mirror, for example, is used as the mirror 75 . This mirror 75 directs part of the near-infrared light incident from the condensing lens 74 toward the mirror 71 and transmits it as it is. As a result, the near-infrared light transmitted through the mirror 75 is reflected by the mirror 71 toward the objective lens 22 and enters the eye E through the objective lens 22 . The near-infrared light reflected by the subject's eye E enters the mirror 71 through the objective lens 22 and is reflected by the mirror 71 toward the mirror 75 . The mirror 75 reflects part of the reflected light incident from the mirror 71 toward the imaging lens 76 .

The imaging lens 76 emits the reflected light incident from the mirror 75 toward the mirror 77 . The mirror 77 reflects part of the reflected light incident from the imaging lens 76 toward the image sensor 78 , and transmits the rest of the reflected light incident from the imaging lens 76 as it is and emits it toward the PSD 79 .

The image sensor 78 is of a CMOS type or a CCD type, and the reflected light reflected by the mirror 77 forms an image of the subject's eye E on its imaging surface. The image sensor 78 captures the image of the subject's eye E formed on the imaging surface and outputs the captured image data 150 (see FIG. 8) to the arithmetic control unit 200 .

Reflected light from the mirror 77 is incident on the light receiving surface of the PSD 79 . The PSD 79 is a sensor capable of detecting the light receiving position of the reflected light on its light receiving surface, and outputs a light receiving signal indicating the light receiving position to the arithmetic control unit 200 . A line sensor may be used instead of the PSD 79 .

The fundus camera unit 2 is provided with two anterior eye cameras 300 . Each anterior segment camera 300 captures an image of the anterior segment Ea from different directions substantially simultaneously. Each anterior segment camera 300 is provided at a position deviated from the optical path of the illumination optical system 10 and the optical path of the imaging optical system 30 . Then, each anterior segment camera 300 acquires a photographed image of the subject's eye E in a state where the subject's eye E is in substantially the same position (orientation). Each photographed image is used by the arithmetic control unit 200 to analyze the three-dimensional position of the characteristic region of the eye E to be examined.

[OCT unit]
The OCT unit 100 includes an optical system used to acquire an OCT image of the fundus oculi Ef. This optical system has a configuration similar to that of a conventional OCT apparatus. That is, this optical system splits low-coherence light into reference light and signal light, causes the signal light that has passed through the fundus oculi Ef and the reference light that has passed through the reference optical path to interfere with each other, and generates interference light. Detect spectral components. This detection result (detection signal) is output from the OCT unit 100 to the arithmetic control unit 200 . Note that the specific configuration of the optical system of the OCT unit 100 is a known technique (see, for example, Patent Documents 1 and 2 above), so a specific description will be omitted here.

[Arithmetic control unit]
FIG. 5 is a functional block diagram of the arithmetic control unit 200. As shown in FIG. As shown in FIG. 5, the arithmetic control unit 200 includes an integrated control section 202, a storage section 204, an image forming section 206, a data processing section 208, and the like. It should be noted that what is described as "- section" in the arithmetic control unit 200 in the present embodiment may be "-- circuit", "-- device", or "-- device". In other words, what is described as "- section" may be composed of firmware, software, hardware, or a combination thereof. In addition, the operation control unit 200 is connected to each part of the fundus camera unit 2 described above, the display device 3, the OCT unit 100, the operation part 210, and the like.

The overall control unit 202 performs overall control of the operations of the retinal camera unit 2 , the display device 3 , and the OCT unit 100 according to input operations to the operation unit 210 by the examiner. Note that FIG. 5 shows only the functions related to the generation and display of the relative position information 219 (see FIG. 11), which will be described later, among the various functions of the integrated control unit 202, and the other functions are known techniques, so they are specifically described. typical illustration is omitted.

The functions of the integrated control unit 202 can be realized using various processors. Various processors include CPU (Central Processing Unit), GPU (Graphics Processing Unit), ASIC (Application Specific Integrated Circuit), and programmable logic devices [for example, SPLD (Simple Programmable Logic Devices), CPLD (Complex Programmable Logic Device), and FPGAs (Field Programmable Gate Arrays)]. Various functions of the integrated control unit 202 may be realized by one processor, or may be realized by a plurality of processors of the same type or different types.

The storage unit 204 stores a control program executed by the processor of the overall control unit 202, image data of an OCT image, image data of a fundus image, eye information (including subject information), and the like. The storage unit 204 also stores correspondence information 212, which will be described later in detail.

The image forming unit 206 analyzes the detection signal input from the OCT unit 100 and forms an OCT image of the fundus oculi Ef. A specific method of forming an OCT image is the same as that of a conventional OCT apparatus. The data processing unit 208 performs image processing and the like on the OCT image formed by the image forming unit 206 and the images (fundus image and anterior segment image) acquired by the fundus camera unit 2 described above.

[Generation and display of relative position information]
The overall control unit 202 executes the control program read out from the storage unit 204 when internal fixation or peripheral fixation is performed in response to the examiner's operation of designating the inspection (imaging) target region on the operation unit 210. , it functions as a fixation target display control unit 214 , a line-of-sight position detection unit 215 , an information generation unit 216 , and a screen display control unit 217 .

The fixation target display control unit 214 performs internal fixation using the target display unit 39 and the objective lens 22, etc., and peripheral fixation using each fixation light 95, based on the examination target site specified by the above-described specifying operation. It controls fixation and external fixation using the external fixation light 96 respectively. Since external fixation is the same as in the conventional art, detailed description will be omitted.

The fixation target display control unit 214 controls the display position of the fixation target on the target display unit 39 based on the examination target region specified by the above-described specifying operation when internal fixation is performed. As a result, the fixation target display control unit 214 shifts the target position, which is the position where the fixation light of the fixation target passes through the objective lens 22, to the optical axis OA of the objective lens 22 (the exit direction of the fixation light). control in the vertical direction (XY direction). That is, the fixation target display control unit 214 controls the emission position of the fixation light emitted from the objective lens 22 toward the eye E to be examined in the above-described vertical direction. Hereinafter, the vertical direction (XY direction) perpendicular to the optical axis OA of the objective lens 22 (the emission direction of the fixation light) is simply referred to as the "optical axis vertical direction".

FIG. 6 is an explanatory diagram showing an example of the relationship between the inspection target portion of the fundus oculi Ef and the display position of the fixation target within the display surface of the target display unit 39. As shown in FIG.

As shown in FIG. 6, the symbol "M" is the display position of the fixation target corresponding to the macula of the fundus Ef of both eyes of the eye E to be examined. Note that this display position M corresponds to the position of the optical axis OA of the objective lens 22 . That is, the fixation light of the fixation target displayed at the display position M passes through the optical axis OA of the objective lens 22 .

The symbol “CR” is the display position of the fixation target corresponding to the center of the fundus Ef of the right eye E to be examined, and the symbol “CL” is the center of the fundus Ef of the left eye E to be examined. is the display position of the fixation target. The symbol “DR” is the display position of the fixation target corresponding to the optic papilla of the fundus Ef of the right eye of the eye E to be examined, and the symbol “DL” is the optic papilla of the fundus Ef of the left eye of the eye E to be examined. is the display position of the fixation target. Symbol “P” is the display position of the fixation target corresponding to the eight positions of the fundus periphery of the fundus Ef of both eyes of the eye E to be examined.

The display position of the fixation target displayed on the target display unit 39 is not limited to the position shown in FIG. 6, and may be changed as appropriate. Also, a display position corresponding to another inspection target site (for example, an intermediate position between the macula and the optic papilla) may be added.

As described above, the fixation light corresponding to the fixation target displayed on the target display unit 39 is projected onto the subject's eye E through the objective lens 22 after passing through the dichroic mirror 46 from the half mirror 39A. This allows the subject's eye E to fixate the fixation light.

When peripheral fixation is performed, the fixation target display control unit 214 selects an inspection target among the fixation lights 95 shown in FIG. Light up the part corresponding to the part.

FIG. 7 is an enlarged front view of the lens accommodating portion 403a. As shown in FIG. 7 and FIG. 6 already described, the fixation light corresponding to the fixation target displayed at the display position M of the target display unit 39 is a visual field within the lens central portion 22a of the objective lens 22, which will be described later. The light is projected onto the subject's eye E through the target position TM (corresponding to the optical axis OA). As a result, the subject's eye E (right eye and left eye) fixes this fixation light, and the macula of the fundus oculi Ef is moved to the irradiation position (scanning position) of the signal light emitted from the OCT unit 100. .

The fixation light corresponding to the fixation target displayed at the display position CR of the target display section 39 is projected onto the subject's eye E through the target position TCR within the lens central portion 22a. Further, the fixation light corresponding to the fixation target displayed at the display position CL of the target display unit 39 is projected onto the subject's eye E through the target position TCL within the lens central portion 22a. As a result, the right eye of the subject's eye E fixes the fixation light that has passed through the target position TCR, or the left eye of the subject's eye E fixes the fixation light that has passed through the target position TCL. As a result, the fundus center of the fundus oculi Ef is moved to the above-described irradiation position of the signal light.

The fixation light corresponding to the fixation target displayed at the display position DR of the target display unit 39 passes through the target position TDR in the lens peripheral portion 22b of the objective lens 22, which will be described later, and is projected onto the subject's eye E. . Further, the fixation light corresponding to the fixation target displayed at the display position DL of the target display section 39 is projected onto the subject's eye E through the target position TDL in the lens peripheral portion 22b. As a result, the right eye of the subject's eye E fixes the fixation light that has passed through the target position TDR, or the left eye of the subject's eye E fixes the fixation light that has passed through the target position TDL. As a result, the optic papilla of the fundus oculi Ef is moved to the irradiation position of the signal light.

The fixation light corresponding to the fixation target displayed at each display position P of the target display section 39 is projected onto the subject's eye E through each target position TP in the lens peripheral portion 22b. As a result, the subject's eye E (right eye and left eye) fixates on the fixation light that has passed through one of the target positions TP, so that any one of the eight fundus peripheral parts of the fundus oculi Ef is already visible. is moved to the irradiation position of the signal light described above.

The lens central portion 22a is an area within a certain range around the optical axis OA of the objective lens 22, and in this embodiment includes the target position TM and the target positions TCR and TCL described above. Here, when the subject's eye E fixes the fixation light that has passed through the target position TM and the target positions TCR and TCL of the objective lens 22, the fixation light is directed to the central region of the visual field range of the subject. It is not necessary to rotate the subject's eye E greatly. Therefore, the subject's eye E can easily fixate on the fixation light. Therefore, the lens central portion 22a is a region in the objective lens 22 in which the subject's eye E can easily fixate on the fixation light.

Note that the lens central portion 22a in the objective lens 22 is not limited to the range shown in FIG. Alternatively, it may be a range including a target position corresponding to another inspection target site (an intermediate position between the macula and the optic papilla, etc.) of the fundus oculi Ef.

The lens peripheral portion 22b is a region outside the lens center portion 22a in the objective lens 22, and includes the target positions TDR, TDL and TP in the present embodiment. When the subject's eye E fixes the fixation light that has passed through the target positions TDR and TDL and the target position TP of the objective lens 22, the fixation light exists in the central region of the visual field range of the subject. Therefore, it is necessary to rotate the subject's eye E largely. Therefore, the subject's eye E may lose sight of the fixation light.

Each fixation lamp 95 for peripheral fixation is arranged so as to surround the objective lens 22 in the lens housing portion 403a, that is, arranged at a position shifted outward in the direction perpendicular to the optical axis from each target position TP. As a result, the subject's eye E (right eye and left eye) fixates on the fixation light emitted from one of the fixation lamps 95, so that eight fundus points corresponding to the above-described internal fixation are observed. Any one of the eight fundus peripheral parts located further outside the peripheral part is moved to the above-described irradiation position of the signal light. When the subject's eye E fixes the fixation light emitted from each fixation lamp 95, it is necessary to rotate the subject's eye E more than when performing internal fixation. There is a risk of losing sight of the fixation light.

Returning to FIG. 5, the correspondence information 212 stored in the storage unit 204 includes a plurality of inspection target regions corresponding to internal fixation and peripheral fixation, and the emission position (XY) of the fixation light for each inspection target region. coordinates) are stored. It should be noted that the emission position of the fixation light for each inspection target region includes each target position on the objective lens 22 corresponding to internal fixation and the position of each fixation light 95 corresponding to peripheral fixation. (See FIG. 7).

The line-of -sight position detection unit 215 constitutes the line-of-sight position detection unit of the present invention together with the line-of-sight position detection optical system 70 described above. The line-of-sight position detection unit 215 turns on the infrared LED 72 when internal fixation or peripheral fixation is started, that is, when fixation light is emitted from the objective lens 22 or the fixation lamp 95 . At the same time, the line-of-sight position detection unit 215 detects the objective lens 22, the fixation lamp 95, etc., based on the captured image data 150 (see FIG. 8) of the subject's eye E input from the image sensor 78 and the received light signal input from the PSD 79. The line-of-sight position of the subject's eye E with respect to is detected.

FIG. 8 is an explanatory diagram for explaining the line-of-sight position detection method (cornea detection method) of the line-of-sight position detection unit 215 using the Purkinje image 151 . As indicated by symbol VIIIA in FIG. 8, near-infrared light from a point light source is incident on the corneal surface of the subject's eye E, and a Purkinje image 151, which is a reflected image of the near-infrared light, is generated. The position of this Purkinje image 151 changes according to the change in the line-of-sight direction of the eye E to be examined.

Therefore, as indicated by symbol VIIIB in FIG. position coordinates C1 of the Purkinje image 151 at Then, the line-of-sight position detection unit 215 detects the line-of-sight direction of the subject's eye E based on the relative position between the position of the Purkinje image 151 indicated by the position coordinates C1 and the center of the pupil. Note that the method of detecting the line-of-sight direction using the Purkinje image 151 is a known technique, and detailed description thereof will be omitted. Further, although the PSD 79 is used in this embodiment, the PSD 79 may be omitted and the position coordinates C1 of the Purkinje image 151 may be detected based only on the captured image data 150 input from the image sensor 78 .

FIG. 9 is an explanatory diagram for explaining a method (scleral reflection method, dark pupil method) for detecting the line-of-sight direction of the eye E to be examined based on the captured image data 150 of the eye E to be examined. In this method, the incidence of the near-infrared light from the point light source on the eye E to be examined can be omitted. After obtaining the imaged image data 150 of the subject's eye E from the image sensor 78 as indicated by symbol IXA in FIG. 150 is binarized with a predetermined brightness threshold. Since the pupil of the subject's eye E has a lower brightness than the surrounding area, when the imaged image data 150 is binarized, the area corresponding to the pupil of the subject's eye E becomes a black pixel area, and the area surrounding the pupil. becomes a white pixel area. Accordingly, the pupil region of the eye E to be examined can be specified from the captured image data 150 of the eye E to be examined.

Then, as indicated by reference numeral IXC in FIG. 9, the line-of-sight position detection unit 215 calculates the center coordinates C2 of the pupil region (black pixel region) of the eye E to be examined from the binarized captured image data 150 of the eye E to be examined. Based on the determined central coordinate C2 and the known geometrical structure of the eyeball, the line-of-sight direction of the subject's eye E is detected. Since detection of the sight line direction by the scleral reflection method (dark pupil method) is a known technique, detailed description thereof will be omitted.

Returning to FIG. 5 , the line-of-sight position detection unit 215 detects the relative position of the subject's eye E with respect to the fundus camera unit 2 based on the captured image data 150 and the known imaging magnification of the imaging optical system 30 . Note that the method for detecting the relative position of the subject's eye E is not particularly limited. Based on the detected relative position and line-of-sight direction of the subject's eye E, the line-of-sight position detection unit 215 detects the line-of-sight on the objective lens 22, the fixation lamp 95, and the peripheral portions thereof, which the subject's eye E is gazing. The position coordinates (XY coordinates) of the position (gazing point) are detected, and the detection result of the position coordinates of the line-of-sight position is output to the information generation unit 216 . Note that the line-of-sight position detection unit 215 repeatedly detects the line-of-sight position of the subject's eye E at regular time intervals, and sequentially outputs detection results of new line-of-sight positions to the information generation unit 216 .

FIG. 10 is an explanatory diagram for explaining generation of the relative position information 219 (see FIG. 11) by the information generation unit 216. As shown in FIG. In FIG. 10, symbol BL indicates a fixation light, symbol SD indicates the line-of-sight direction of the eye E to be examined, and symbol SP indicates the line-of-sight position of the eye E to be examined. Also, in FIG. 10, description will be made assuming that the fixation light is emitted from the target position TDR of the objective lens 22 (other target position or each fixation lamp 95 is also possible).

As shown in FIG. 10, the information generator 216 generates relative position information 219 (see FIG. 11) when internal fixation or peripheral fixation is started. The relative position information 219 is the relative position of the line-of-sight position of the subject's eye E in the direction perpendicular to the optical axis relative to the emission position of the fixation light emitted from the objective lens 22 and the fixation light 95; This is information indicating the direction of deviation and the amount of deviation Δd.

The information generation unit 216 first refers to the correspondence information 212 in the storage unit 204 described above based on the designation operation of the inspection target site of the fundus oculi Ef input to the operation unit 210 to determine the inspection target site. The emission position of the fixation light (here, target position TDR) is determined. Next, the information generation unit 216 generates relative position information 219 (see FIG. 11) based on the line-of-sight position of the subject's eye E detected by the line-of-sight position detection unit 215 and the emission position of the fixation light. Position information 219 is output to screen display control unit 217 .

FIG. 11 is an explanatory diagram showing a first example of the relative position information 219. As shown in FIG. As shown in FIG. 11, the first example of the relative position information 219 is the first image of the present invention centered (origin) on the exit position of the fixation light. The relative position information 219 includes a mark ML indicating the emission position of the fixation light and a mark ME indicating the line-of-sight position of the eye E to be examined.

Based on the emission position of the fixation light and the line-of-sight position of the eye E, the information generator 216 calculates the shift direction and amount Δd of the line-of-sight position from the emission position in the direction perpendicular to the optical axis. Then, based on this calculation result, the information generation unit 216 determines the mark ML provided at the center position of the image and the mark ML provided at a position separated from the center position of the image by a distance corresponding to the displacement amount Δd in the above-described displacement direction. The relative position information 219 including the mark ME is generated. As a result, from the relative position information 219, the fixation state of the eye to be examined E (whether or not the eye to be examined catches the fixation light, where the line of sight of the eye to be examined E is directed with respect to the fixation light, etc.) can be obtained. ) can be determined.

FIG. 12 is an explanatory diagram showing a second example of the relative position information 219. As shown in FIG. As shown in FIG. 12, the second example of the relative position information 219 is based on the optical axis OA of each of the emission position of the fixation light and the line-of-sight position of the subject's eye E with respect to the optical axis OA (origin). Fig. 2 is a second image of the present invention showing vertical relative positions; That is, the second example of the relative position information 219 is an image that indirectly indicates the relative position of the line-of-sight position in the direction perpendicular to the optical axis with respect to the emission position. This relative position information 219 includes a mark MO indicating the optical axis OA in addition to the already-described mark ML and mark ME.

The information generation unit 216 calculates the position of the optical axis OA based on the emission position of the fixation light, the line-of-sight position of the eye to be examined E, and the position of the optical axis OA corresponding to the target position TM (see FIG. 7). and a second direction and amount of deviation of the line-of-sight position with respect to the position of the optical axis OA. Then, based on each calculation result, the information generation unit 216 determines the mark MO provided at the center position of the image and the mark MO provided at a position separated from the center position of the image by a distance corresponding to the first displacement amount in the first displacement direction. Relative position information 219 including the mark ML and the mark ME provided at a position separated from the image center position by a distance corresponding to the second shift amount in the second shift direction is generated. Accordingly, from the relative position information 219, in addition to the above-described fixation state of the eye E to be inspected, it is possible to determine the emission position and the line-of-sight position with reference to the optical axis OA.

Returning to FIG. 5 , the information generation unit 216 sequentially updates the relative position information 219 each time a new detection result of the sight line position of the subject's eye E is input from the sight line position detection unit 215 . As a result, when the line-of-sight position of the subject's eye E moves toward the emission position of the fixation light, the position of the mark ME in the relative position information 219 is updated accordingly, and the mark ME moves toward the mark ML. do. Then, the information generation unit 216 sequentially outputs new relative position information 219 to the screen display control unit 217 each time the relative position information 219 is updated.

The screen display control unit 217 performs display control of the display device 3 . The screen display control unit 217 causes the display device 3 to display the relative position information 219 input from the information generation unit 216 when internal fixation or peripheral fixation is started. Therefore, the screen display control section 217 functions as an output section of the present invention.

Further, the screen display control unit 217 generates a photographed screen 220 (see FIG. 13, etc.) corresponding to various operations executed by the ophthalmologic apparatus 1 at the same time as internal fixation or peripheral fixation, and displays this photographed screen 220. It is displayed on the device 3. In this case, the screen display control unit 217 causes the display device 3 to display the photographing screen 220 and the relative position information 219 in a superimposed manner.

Types of operations of the ophthalmologic apparatus 1 that are performed simultaneously with internal fixation or peripheral fixation include, for example, alignment of the retinal camera unit 2 with respect to the anterior segment Ea, focus adjustment of the retinal camera unit 2 with respect to the fundus oculi Ef, and 1 auto-optimization (auto-optimization), etc. can be given as an example. Note that the alignment here is automatic alignment, but manual alignment may also be performed. Auto-optimization performs fine adjustment of the position of the retinal camera unit 2 in the Z direction, sensitivity adjustment of the OCT image, and the like.

FIG. 13 is an explanatory diagram showing an example of the photographing screen 220 and the relative position information 219 superimposed on the display device 3 during alignment of the retinal camera unit 2. As shown in FIG. FIG. 14 is an explanatory diagram showing an example of the photographing screen 220 and the relative position information 219 superimposed on the display device 3 when the focus of the retinal camera unit 2 is adjusted. FIG. 15 is an explanatory diagram showing an example of the photographing screen 220 and the relative position information 219 superimposed on the display device 3 during auto-optimization of the ophthalmologic apparatus 1 .

As shown in FIG. 13 , the screen display control unit 217 acquires an anterior segment image (observation image) of the anterior segment Ea from the retinal camera unit 2 during alignment of the retinal camera unit 2 . Then, the screen display control unit 217 generates a photographed screen 220 including an anterior segment image observation screen 220a that is an observation screen of an anterior segment image, and superimposes the photographed screen 220 and the relative position information 219 on the display device 3. display.

As shown in FIGS. 14 and 15, the screen display control unit 217 controls the focus adjustment of the retinal camera unit 2 or auto-optimization of the ophthalmologic apparatus 1 from the retinal camera unit 2 in addition to the anterior ocular image described above. A fundus image (observation image) of the fundus oculi Ef is obtained, and an OCT image (observation image) is obtained from the image forming unit 206 . Then, the screen display control unit 217 generates a photographing screen 220 including an anterior segment image observation screen 220a, a fundus image observation screen 220b as a fundus image observation screen, and an OCT image observation screen 220c as an OCT image observation screen. Then, the photographing screen 220 and the relative position information 219 are superimposed on the display device 3 .

Note that the display position, display range, and the like of the relative position information 219 within the photographing screen 220 are not particularly limited. Further, when the ophthalmologic apparatus 1 is provided with a plurality of display devices 3, the screen display control unit 217 causes the display device 3 different from the display device 3 that displays the imaging screen 220 to display the relative position information 219. may Furthermore, in the present embodiment, the photographing screen 220 displayed on the display device 3 during alignment, focus adjustment, and auto-optimization has been described as an example. The superimposed display of various photographing screens 220 and relative position information 219 may also be performed when setting the amount of illumination light, etc.).

[Operation of Ophthalmic Device]
FIG. 16 is a flow chart showing the examination process of the eye to be examined E by the ophthalmologic apparatus 1 configured as described above, particularly the flow of the display process of the relative position information 219 on the display device 3 (corresponding to the operating method of the ophthalmologic apparatus of the present invention).

As shown in FIG. 16, after the predetermined examination preparation process in the ophthalmologic apparatus 1 is completed, the examiner operates the operation unit 210 to specify the examination target portion of the fundus oculi Ef (step S1). When this designation is made, the integrated control unit 202 controls each unit of the ophthalmologic apparatus 1 to set the light amount of each illumination light of the illumination optical system 10 and the photographing optical system 30 by a known method (step S2 ), alignment of the retinal camera unit 2 (step S3), focus adjustment of the retinal camera unit 2 (step S4), and auto-optimization of the ophthalmologic apparatus 1 (step S5) are sequentially executed.

On the other hand, the fixation target display control unit 214 of the integrated control unit 202 displays the fixation target on the target display unit 39 based on the inspection target site specified by the specifying operation when internal fixation is performed. The image is displayed at the corresponding display position (see FIG. 6), and the fixation lamp 95 corresponding to the inspection target site is turned on when peripheral fixation is performed. As a result, when internal fixation is performed, the fixation light is emitted from the target position (see FIG. 7) corresponding to the inspection target site of the objective lens 22, and when peripheral fixation is performed, it corresponds to the inspection target site. A fixation light is emitted from the fixation lamp 95 (step S6). As a result, internal fixation or peripheral fixation is initiated.

In addition, in response to the start of internal fixation or peripheral fixation, the line-of-sight position detection unit 215 turns on the infrared LED 72, and also receives captured image data 150 of the subject's eye E input from the image sensor 78 and the PSD 79. A received light signal is acquired.

Next, based on the captured image data 150, the received light signal, and the known imaging magnification of the imaging optical system 30, the line-of-sight position detection unit 215 detects the object lens 22 and each of the objective lens 22 and each of which the subject's eye E is gazing by using the above-described method. The line-of-sight position of the subject's eye E with respect to the fixation lamp 95 or the like is detected (step S7). Then, the line-of-sight position detection unit 215 outputs the detection result of the line-of-sight position of the subject's eye E to the information generation unit 216 .

Further, when internal fixation or peripheral fixation starts, the information generation unit 216 refers to the correspondence information 212 in the storage unit 204 to determine the emission position of the fixation light corresponding to the inspection target site. Then, the information generating unit 216 generates the relative position information shown in FIGS. 219, and outputs this relative position information 219 to the screen display control unit 217 (step S8).

Based on various images acquired from the retinal camera unit 2 and the relative position information 219 acquired from the information generation unit 216, the screen display control unit 217 controls the display device as shown in FIGS. 3 to superimpose the shooting screen 220 and the relative position information 219 (step S9). Accordingly, the examiner can determine the fixation state of the subject's eye E based on the relative position information 219 displayed on the display device 3 . Therefore, for example, even if the subject's eye E loses sight of the fixation light, the examiner can easily determine where the line of sight of the subject's eye E is directed with respect to the fixation light by referring to the relative position information 219. can be discriminated. As a result, the examiner can appropriately call attention to the examinee.

Thereafter, the processes from step S7 to step S9 are repeatedly executed until the auto-optimization in step S5 is completed, that is, until the preparation for the actual imaging of the examination target region is completed (NO in step S10). ). As a result, even if the subject's eye E loses sight of the fixation light during alignment, focus adjustment, auto-optimization, or the like, the examiner can easily determine this from the relative position information 219 . Therefore, the examiner can appropriately call attention to the examinee. As a result, the data of the fundus oculi Ef can be obtained (actual photographing) while the subject's eye E is reliably fixating on the fixation light.

When step S5 is completed (YES in step S10), a fundus image (actually captured image) and an OCT image (actually captured image) of the fundus oculi Ef are captured by the retinal camera unit 2, OCT unit 100, etc. by a known method. (step S11).

Thereafter, when changing the inspection target region, the above-described processes from step S1 to step S11 are repeatedly executed (step S12).

[Effect of this embodiment]
As described above, in this embodiment, when internal fixation and peripheral fixation are performed, the line-of-sight position of the subject's eye E is detected, and the line-of-sight position of the subject's eye E with respect to the emission position of the fixation light is detected in the direction perpendicular to the optical axis. Since the relative position information 219 indicating the relative position of the eye E is generated, the examiner can easily determine the fixation state of the eye E to be examined based on the relative position information 219 .

[Another embodiment of the ophthalmic device]
In the ophthalmologic apparatus 1 of the above embodiment, the relative position information 219 is always displayed on the display device 3 when internal fixation and peripheral fixation are performed. Whether or not to display the relative position information 219 on the display device 3 is switched according to the viewing state. Note that the ophthalmologic apparatus 1 of another embodiment has basically the same configuration as the ophthalmologic apparatus 1 of the above embodiment. omitted.

FIG. 17 is a flow chart showing the flow of examination processing for the subject's eye E by the ophthalmologic apparatus 1 of another embodiment, particularly display processing of the relative position information 219 on the display device 3 . Note that each process up to step S8 is the same as that of the above-described embodiment described with reference to FIG. 16, and therefore description thereof is omitted here.

Based on the relative position information 219 acquired from the information generation unit 216, the screen display control unit 217 of another embodiment controls the shift amount Δd (Fig. 10 ) is greater than a predetermined threshold (step S8A). Then, when the shift amount Δd becomes larger than the threshold value, the screen display control unit 217 causes the display device 3 to display the shooting screen 220 and the relative position information 219 in a superimposed manner (NO in step S8A, step S9). Thereby, the same effects as those of the above-described embodiment can be obtained.

On the other hand, when the shift amount Δd is equal to or less than the threshold, the screen display control unit 217 causes the display device 3 to display only the shooting screen 220 and omit the display of the relative position information 219 by the display device 3 (step S8A). YES). As a result, when the fixation state of the subject's eye E is good, the display of the relative position information 219 by the display device 3 is omitted. is prevented.

[others]
In each of the above-described embodiments, the relative position information 219 generated by the information generation unit 216 is displayed on the display device 3, but the relative position information 219 is output by voice from an audio output device (output unit of the present invention) such as a speaker. You can output.

The line-of-sight position detection method by the line-of-sight position detection unit 215 in each of the above-described embodiments is not limited to the methods described with reference to FIGS. 8 and 9 . For example, a method using the positional relationship between a reference point such as the inner corner of the eye of the examiner and a moving point such as the iris of the eye to be examined E, and a method of detecting the movement of the eye to be examined E using an electro-oculography sensor, etc. Detection methods can be used.

In each of the above embodiments, the ophthalmic apparatus 1 capable of performing both internal fixation and peripheral fixation has been described as an example. The present invention can also be applied to the device 1 .

In each of the above-described embodiments, a multifunction machine of an optical coherence tomography and a retinal camera was described as an example of the ophthalmologic apparatus 1, but the optical coherence tomography, retinal camera, scanning laser ophthalmoscope, laser treatment apparatus The present invention can be applied to various ophthalmologic devices for fixation of the subject's eye E, such as a photocoagulator), a corneal endothelial cell testing device, a non-contact intraocular pressure testing device, an autoreflection keratometer, and a perimeter.

1 ... Ophthalmic device,
2 ... fundus camera unit,
3 ... display device,
10... illumination optical system,
22 ... objective lens,
30 ... photographing optical system,
39 ... optotype display unit,
70 line-of-sight position detection optical system,
95... fixation light,
100 ... OCT unit,
200 operation control unit,
202 ... integrated control unit,
210 operation unit,
214 ... fixation target display control unit,
215 line-of-sight position detector,
216 ... information generation unit,
217 screen display control unit,
219 relative position information,
220... Shooting screen

Claims (9)

a fixation light emitting section for emitting fixation light;
a line-of-sight position detection unit that detects a line-of-sight position of the subject's eye with respect to the fixation light emitting unit;
When the direction perpendicular to the emission direction of the fixation light emitted from the fixation light emitting section is defined as the vertical direction, the detection result of the sight line position detecting section and the direction of the fixation light emitted from the fixation light emitting section an information generation unit for generating relative position information indicating the relative position of the line-of-sight position in the vertical direction with respect to the emission position, based on the emission position of the fixation light;
with
The ophthalmologic apparatus, wherein the relative position information includes a mark indicating the emission position and a mark indicating the relative position of the line-of-sight position in the vertical direction with respect to the emission position . The ophthalmologic apparatus according to claim 1, further comprising an output unit that displays the relative position information generated by the information generation unit. Based on the relative position information generated by the information generating unit, the output unit detects that the relative position information 3. The ophthalmologic apparatus according to claim 2, wherein display is executed, and display of the relative position information is omitted when the deviation amount is equal to or less than the threshold value. The information generating unit generates a first image that is a first image showing the relative position information and centered on the emission position,
The ophthalmologic apparatus according to claim 2 or 3, wherein the output section displays the first image. an optical system for irradiating the eye to be inspected with illumination light through an objective lens having an optical axis parallel to the emission direction and for receiving reflected light of the illumination light reflected by the eye to be inspected;
The information generating unit generates, as the relative position information, a second image centered on the optical axis and indicating relative positions in the vertical direction of each of the emission position and the line-of-sight position with respect to the optical axis. generate the image,
The ophthalmologic apparatus according to claim 2 or 3, wherein the output section displays the second image. wherein the fixation light emitting portion selectively emits the fixation light from a plurality of the emission positions;
An operation unit that receives an operation for specifying the emission position,
The ophthalmologic apparatus according to any one of claims 1 to 5, wherein the information generating section generates the relative position information corresponding to the emission position selected by the specifying operation on the operating section. The fixation light emitting unit includes a target display unit that displays a fixation target, and the fixation target corresponding to the fixation target displayed on the target display unit through an objective lens having an optical axis parallel to the emission direction. The ophthalmologic apparatus according to any one of claims 1 to 6, further comprising a projection optical system that projects fixation light onto the subject's eye. an optical system for irradiating the eye to be inspected with illumination light through an objective lens having an optical axis parallel to the emission direction and for receiving reflected light of the illumination light reflected by the eye to be inspected;
8. The ophthalmologic apparatus according to any one of claims 1 to 7, wherein the fixation light emitting section comprises a plurality of fixation lights surrounding the objective lens. In a method for operating an ophthalmologic device having a fixation light emitting portion that emits fixation light,
A line-of-sight position detection unit detects a line-of-sight position of the subject's eye with respect to the fixation light emitting unit,
When the information generation unit sets the direction perpendicular to the emission direction of the fixation light emitted from the fixation light emission unit as the vertical direction, the detection result of the sight line position detection unit and the fixation light generating relative position information indicating a relative position of the line-of-sight position in the vertical direction with respect to the emission position, based on the emission position of the fixation light emitted from the emission unit;
A method of operating an ophthalmologic apparatus, wherein the relative position information includes a mark indicating the emission position and a mark indicating the relative position of the line-of-sight position in the vertical direction with respect to the emission position .

Images