JP2020146375A - Ophthalmologic apparatus and operation method thereof - Google Patents

Abstract

To provide an ophthalmologic apparatus capable of reliably protecting a subject's eye from light hazard, and an operation method thereof.SOLUTION: An ophthalmologic apparatus comprises: an irradiation system for irradiating a subject's eye with light exited from a light source; a drive condition acquisition unit that acquires a drive condition of the light source relating to intensity of the light exited from the light source and, when the drive condition is changeable, acquires the drive condition each time at least the drive condition is changed; an irradiation time measuring unit for continuously measuring a cumulative irradiation time of the light to the subject's eye; and an irradiation light quantity estimation unit continuously estimating an irradiation quantity of light to be applied to the subject's eye based on the acquisition result of the drive condition acquisition unit and the measurement result of the irradiation time measuring unit.SELECTED DRAWING: Figure 3

Description

The present invention relates to an ophthalmic apparatus that irradiates an eye to be inspected with light and a method of operating the same.

In ophthalmology, for example, a slit lamp microscope (also called a slit lamp), an OCT (Optical Coherence Tomography) device, a fundus camera, and an SLO (Scanning Laser Ophthalmoscope) are used to illuminate the eye to be inspected (observation light). Alternatively, an ophthalmic apparatus that irradiates various types of light such as examination light is provided.

Standards that specify the safety requirements for light irradiation of the eye to be inspected, such as standards for protection from light hazards, are applied to such ophthalmic devices. This standard is stipulated in, for example, ISO (International Organization for Standardization) 15004-2: 2007 (Ophthalmic Instruments --Fundamental Requirements And Test Methods --Part2: light hazard protection) (JIS T 15004-2: 2013).

In Patent Document 1, the luminous intensity of the slit light emitted from the illumination light source is measured, and the illumination light source is controlled so that the luminous intensity does not exceed a predetermined maximum luminous intensity value, or the luminous intensity is larger than the maximum luminous intensity value. A narrow-gap light source that displays a warning or the like when this happens is described.

Further, Patent Document 2 describes a multifunction device that combines an ophthalmic microscope that irradiates an eye to be inspected with illumination light and an OCT device that irradiates the eye to be inspected with measurement light. The composite machine described in Patent Document 2 depends on the operation mode so that the light amount of the illumination light and the combined light of the measurement light is equal to or less than the default value, for example, based on the detection result of the light amount detection unit that detects the light amount of the measurement light. The amount of illumination light or measurement light is controlled.

Japanese Unexamined Patent Publication No. 2018-187064 Japanese Unexamined Patent Publication No. 2017-012432

In order to protect the eye to be inspected from optical hazards, it is desirable to keep the amount of light (also referred to as the amount of exposure) of the light applied to the eye to be inspected to be less than the maximum permissible amount defined in the above ISO standards and the like. Here, the irradiation light amount of light is a physical quantity obtained by time-integrating the intensity of light (the amount of light per unit time in a unit area) irradiating the eye to be inspected. Then, the amount of the irradiation light increases or decreases according to the length of the integrated irradiation time of the light to the eye to be inspected, in addition to increasing or decreasing according to the magnitude of the intensity of the light applied to the eye to be inspected. Therefore, even if only the luminosity of the slit light emitted from the illumination light source is controlled or monitored as described in Patent Document 1, if the integrated irradiation time of the slit light for the eye to be examined becomes long, the slit for the eye to be examined The amount of light irradiation may increase significantly.

Further, in Patent Document 2, the "light intensity" and the "intensity" of light are equated with each other, and substantially only the intensity detection of the synthetic light is performed as the light intensity detection of the synthetic light (see paragraph [0017]). ). Therefore, even in the apparatus described in Patent Document 2, if the integrated irradiation time of the synthetic light to the eye to be inspected becomes long, the amount of the synthetic light to irradiate the eye to be inspected may increase remarkably.

As described above, since the various ophthalmic devices described in Patent Document 1 and Patent Document 2 do not consider the integrated irradiation time of the light emitted to the eye to be inspected, the amount of light to be irradiated to the eye to be inspected must be accurately obtained. I can't. For this reason, it has been desired to develop an ophthalmic apparatus capable of reliably protecting the eye to be inspected from optical hazards.

The present invention has been made in view of such circumstances, and an object of the present invention is to provide an ophthalmic apparatus capable of reliably protecting an eye to be inspected from optical hazards and a method of operating the same.

An ophthalmic apparatus for achieving the object of the present invention is an irradiation system that irradiates an eye to be inspected with light emitted from a light source, and a drive condition acquisition unit that acquires a drive condition of the light source related to the intensity of light emitted from the light source. However, when the driving conditions can be changed, at least the driving condition acquisition unit that acquires the driving conditions each time the driving conditions are changed, and the irradiation that continuously measures the integrated irradiation time of the light to the eye to be inspected. It includes a time measuring unit, an irradiation light amount estimation unit that continuously estimates the irradiation light amount of the light irradiated to the eye to be inspected based on the acquisition result of the driving condition acquisition unit and the measurement result of the irradiation time measuring unit.

According to this ophthalmic apparatus, it is possible to estimate the amount of light to be irradiated to the eye to be inspected in consideration of the integrated irradiation time of the light to be irradiated to the eye to be inspected.

The ophthalmic apparatus according to another aspect of the present invention includes a warning information notification unit that notifies warning information when the irradiation light amount estimated by the irradiation light amount estimation unit becomes larger than a predetermined upper limit value. As a result, the warning information of the optical hazard of the eye to be inspected can be notified to the examiner, so that the eye to be inspected can be reliably protected from the optical hazard.

The ophthalmic apparatus according to another aspect of the present invention includes an irradiation light amount notification unit that notifies the irradiation light amount estimated by the irradiation light amount estimation unit. As a result, the examiner can be notified of the amount of light emitted to the eye to be inspected.

In the ophthalmic apparatus according to another aspect of the present invention, the ophthalmic apparatus includes a storage unit that stores in advance the correspondence between the driving condition and the intensity of the light applied to the eye to be inspected, and the irradiation light amount estimation unit is the driving condition acquisition unit. Based on the acquisition result, the light intensity is determined by referring to the correspondence in the storage unit, and the irradiation light amount is estimated based on the light intensity and the measurement result of the irradiation time measurement unit. This makes it possible to estimate the amount of light emitted to the eye to be inspected using the driving conditions of the light source.

The ophthalmic apparatus according to another aspect of the present invention includes an motion detection unit for detecting the on / off of the light source, and the irradiation time measuring unit calculates the time when the light source is turned on based on the detection result of the motion detection unit. Measure as. As a result, the integrated irradiation time can be measured accurately.

In the ophthalmic apparatus according to another aspect of the present invention, the irradiation time measuring unit includes a support mechanism for supporting the irradiation system relative to the eye to be inspected and a position detecting unit for detecting the position of the irradiation system. Based on the detection result of the position detection unit, the time during which the position of the irradiation system is set within the predetermined range of the irradiation position of light for the eye to be inspected is measured as the integrated irradiation time. As a result, the integrated irradiation time can be measured accurately.

The ophthalmic apparatus according to another aspect of the present invention includes a chin support for supporting the face of the subject and a face detection unit for detecting the presence or absence of support of the face by the chin support, and the irradiation time measuring unit is a face. Based on the detection result of the detection unit, the time during which the chin rest supports the face is measured as the integrated irradiation time. As a result, the integrated irradiation time can be measured accurately.

In the ophthalmic apparatus according to another aspect of the present invention, the anterior eye based on the photographed image for each of the photographing system for continuously photographing the anterior segment of the eye to be inspected and the captured image of the anterior segment captured by the imaging system. A light irradiation detection unit for detecting whether or not light is being irradiated to the unit is provided, and the irradiation time measurement unit measures the integrated irradiation time based on the detection result of the light irradiation detection unit for each captured image. .. As a result, the integrated irradiation time can be measured accurately.

In the ophthalmic apparatus according to another aspect of the present invention, irradiation for detecting the irradiation position of light in the photographed image for each photographed image of the anterior eye portion irradiated with light based on the detection result of the light irradiation detection unit. A position detection unit is provided, and the irradiation time measurement unit continuously measures the integrated irradiation time for each of a plurality of regions in the captured image based on the detection result of the irradiation position detection unit, and the irradiation light amount estimation unit acquires the driving condition. The irradiation light amount for each of a plurality of regions is continuously estimated based on the acquisition result of the unit and the measurement result of the irradiation time measurement unit for each of a plurality of regions. As a result, the examiner can easily grasp the amount of irradiation light for each of the plurality of regions, so that all the regions of the anterior segment of the eye to be inspected can be reliably protected from optical hazards.

In the ophthalmic apparatus according to another aspect of the present invention, the irradiation light amount estimation unit estimates based on the detection results of the wavelength range detection unit that detects the wavelength range of the light emitted to the eye to be inspected and the wavelength range detection unit. It is provided with a multiplication unit for multiplying the amount of irradiation light by a predetermined coefficient for each wavelength region. As a result, the eye to be inspected can be reliably protected from optical hazards regardless of the wavelength range of the light applied to the eye to be inspected.

In the ophthalmic apparatus according to another aspect of the present invention, the drive condition acquisition unit acquires the drive voltage value or the drive current value of the light source as the drive condition.

A method of operating an ophthalmic apparatus for achieving the object of the present invention is a method of operating an ophthalmic apparatus including an irradiation system for irradiating a subject eye with light emitted from a light source, wherein the light source relates to the intensity of light emitted from the light source. The drive condition acquisition step for acquiring the drive condition, and when the drive condition can be changed, at least the drive condition acquisition step for acquiring the drive condition each time the drive condition is changed, and the light for the eye to be inspected. The amount of light emitted to the eye to be inspected is continuously estimated based on the acquisition result of the irradiation time measurement step for continuously measuring the integrated irradiation time, the acquisition result of the driving condition acquisition step, and the measurement result of the irradiation time measurement step. It has an irradiation light amount estimation step.

In the method of operating the ophthalmic apparatus according to another aspect of the present invention, there is a warning information notification step for notifying warning information when the irradiation light amount estimated in the irradiation light amount estimation step becomes larger than a predetermined upper limit value.

The present invention can reliably protect the eye to be inspected from optical hazards.

It is a side view of a slit lamp microscope. It is the schematic which showed the structure of each optical system of an illumination system, an observation system, and an imaging system. It is a functional block diagram of the control part of 1st Embodiment. It is explanatory drawing for demonstrating the 1st example of the detection part. It is explanatory drawing for demonstrating the 2nd example of the detection part. It is explanatory drawing for demonstrating the 3rd example of the detection part. It is explanatory drawing for demonstrating the estimation of the irradiation light amount of a gap light by an irradiation light amount estimation part. It is explanatory drawing for demonstrating the notification of the irradiation light amount of a gap light. It is explanatory drawing for demonstrating the notification of the warning information of an optical hazard. It is a flowchart which shows the flow | flow of the estimation of the irradiation light amount of the slit light by the slit lamp microscope, and the notification of the warning information of an optical hazard. It is a functional block diagram of the control part of the slit lamp microscope of the 2nd Embodiment. It is explanatory drawing for demonstrating the function of the light irradiation detection part. It is explanatory drawing for demonstrating the measurement of the integrated irradiation time of the gap light by the irradiation time measuring part of 2nd Embodiment. It is a functional block diagram of the control part of the slit lamp microscope of the 3rd Embodiment. It is explanatory drawing which showed an example of the integrated map image generated by the control part of 3rd Embodiment. It is a functional block diagram of the control part of the slit lamp microscope of 4th Embodiment. It is explanatory drawing for demonstrating an example of a display part. It is a schematic diagram of the apparatus main body of the ophthalmic apparatus of this invention which is different from a slit lamp microscope.

[First Embodiment]
<Structure of slit lamp microscope>
FIG. 1 is a side view of the slit lamp microscope 10 placed on the table 9. This slit lamp microscope 10 corresponds to the ophthalmic apparatus of the present invention, and is used for various observations such as corneal observation, fundus observation, and crystalline lens observation of the eye E to be inspected.

As shown in FIG. 1, the slit lamp microscope 10 includes a main body base 11, a jaw cradle 12, an electric drive unit 13, a moving stage 14, an operation lever 15, a support unit 16, and an illumination system 18. , The observation system 19 and the control unit 20.

The main body base 11 is placed on the table 9. A chin cradle 12 is provided at the end of the main body base 11 on the subject side. Further, an electric drive unit 13 and a moving stage 14 are provided on the upper surface of the main body base 11.

The chin cradle 12 has a chin rest 12a and a forehead pad 12b whose positions can be adjusted in the vertical direction in the drawing, and supports the face of the subject when observing the eye E to be inspected with the slit lamp microscope 10.

The electric drive unit 13 movably holds the moving stage 14 in the horizontal direction (front-back direction and left-right direction) on the main body base 11. Further, an operation lever 15 and a support portion 16 are provided on the upper surface of the moving stage 14. The anteroposterior direction is the front direction toward the subject and the rear direction away from the subject, and the left-right direction is the eye width direction of the subject.

The electric drive unit 13 includes a motor (not shown) and a drive transmission mechanism (not shown) that converts the rotation of the motor into a driving force in the horizontal direction. The electric drive unit 13 moves the moving stage 14 in the horizontal direction in response to the operation of the operation lever 15 under the control of the control unit 20 described later. As a result, the position of the support portion 16 (illumination system 18 and observation system 19) with respect to the eye E to be inspected can be adjusted, and the illumination system 18 and the like can be moved relative to the eye E to be inspected. The support mechanism of the present invention is configured together with the moving stage 14, the support portion 16 and the support arm 23 described later.

The operating lever 15 is provided at the end of the moving stage 14 on the examiner side. The operation lever 15 is an operation member for moving the support portion 16 (illumination system 18 and observation system 19) in the front-rear direction and the left-right direction. For example, by tilting the operating lever 15 in the front-rear direction or the left-right direction, the electric drive unit 13 moves the moving stage 14 in the front-rear direction or the left-right direction under the control of the control unit 20 described later. Although not shown, a switch used for photographing the eye E to be inspected is provided on the top of the operation lever 15.

The support portion 16 supports the illumination system 18 and the observation system 19, respectively. A support arm 22 that supports the observation system 19 is attached to the support portion 16 so as to be rotatable in the left-right direction (rotatably around an axis parallel to the vertical direction). The support arm 22 has a horizontal portion extending in the front-rear direction in the drawing, and a vertical portion extending upward from a base end portion on the rear side of the horizontal portion. A support arm 23 that supports the lighting system 18 is rotatably attached to the upper surface of the horizontal portion of the support arm 22 in the left-right direction. Further, the lens barrel main body 24 of the observation system 19 is attached to the upper surface of the vertical portion of the support arm 22.

The support arm 22 and the support arm 23 are independently rotatable coaxially. As a result, the examiner manually rotates the support arm 22 to swing the observation system 19 in the left-right direction about the rotation axis of the support arm 22, and the support arm 23 is manually rotated. The lighting system 18 is swung in the left-right direction about the rotation axis of the support arm 23. The support arms 22 and 23 may be rotated by a drive unit composed of a motor and a drive transmission mechanism.

The illumination system 18 corresponds to the irradiation system of the present invention, and irradiates the eye E to be inspected with various types of light including the gap light L1 (corresponding to the light of the present invention, see FIG. 2). As described above, the illumination system 18 arbitrarily changes the incident position (irradiation position) of the gap light L1 with respect to the eye E to be inspected by manually swinging it in the left-right direction around the rotation axis of the support arm 23. It is possible. The illumination system 18 may be configured to be swingable in the vertical direction in order to adjust the depression angle and the elevation angle of the gap light L1 incident on the eye E to be inspected.

At a position below the illumination system 18, a mirror 25 that reflects the gap light L1 and the like output from the illumination system 18 toward the eye E to be inspected is arranged. Since the slit lamp microscope 10 of the present embodiment is a Zeiss type (Littmann type), the mirror 25 is arranged below the illumination system 18, but the slit lamp microscope 10 is of the Haag type (Goldman type). In some cases, the mirror 25 may be arranged above the lighting system 18.

The observation system 19 transmits the reflected light L2 (see FIG. 2) reflected by the eye E to be examined in response to the incident of the gap light L1 (see FIG. 2) on the eye E to be described in the eyepiece 24a described later. It has a pair of left and right optical systems that lead to the eyepiece 48 (see FIG. 2). The reflected light L2 includes various types of light that have passed through the eye E to be inspected, such as scattered light.

The observation system 19 is housed in the lens barrel main body 24. The end of the lens barrel body 24 is a binocular eyepiece 24a. The examiner binocularly views the anterior segment image 27 (see FIG. 2) of the eye E to be inspected through the eyepiece 24a. By manually swinging the observation system 19 in the left-right direction about the rotation axis of the support arm 22 as described above, the observation direction of the eye E to be inspected by the observation system 19 can be changed.

On the side surface of the lens barrel main body 24, an observation magnification operation knob 28 for changing the observation magnification of the eye E to be inspected is arranged. Further, the lens barrel main body 24 is provided with an imaging system 29 for photographing the anterior segment of the eye to be inspected E through the observation system 19.

The control unit 20 is an arithmetic unit such as a computer connected to each part of the slit lamp microscope 10, and comprehensively controls the operation of each part of the slit lamp microscope 10. Although the control unit 20 is provided outside the housing of the slit lamp microscope 10 in the drawing, it may be provided inside the housing.

FIG. 2 is a schematic view showing the configurations of each optical system of the illumination system 18, the observation system 19, and the photographing system 29. The reference numeral Eo indicates the observation eye of the examiner, the reference numeral O1 indicates the optical axis of the gap light L1 (illumination light) in the illumination system 18, and the reference numeral O2 indicates the optical axis of the reflected light L2 in the observation system 19.

<Construction of lighting system>
The illumination system 18 includes a light source 31, a relay lens 32, an illumination diaphragm 33, a condenser lens 34, a field diaphragm 35, a gap forming portion 36, and a condenser lens 37. Further, in the illumination system 18, an optical filter 38 is removably arranged between the gap forming portion 36 and the condensing lens 37.

The light source 31 emits illumination light, which is white light, toward the relay lens 32. As the light source 31, a known white light source that emits white light such as a halogen lamp, an LED (light emitting diode) light source, and a laser light source is used. As the light source 31, a flash light source and a dedicated light source for corneal observation or fundus observation may be separately provided.

The relay lens 32 emits the illumination light incident from the light source 31 toward the illumination diaphragm 33.

The illumination diaphragm 33 has a translucent portion that transmits the illumination light incident from the light source 31, and the size (aperture diameter) of the translucent portion can be changed. The illumination diaphragm 33 is an optical member that adjusts the amount of illumination light (gap light L1 or the like) emitted from the illumination system 18 to the eye E to be inspected, that is, the brightness by adjusting the aperture diameter. Further, the illumination diaphragm 33 also has a function of reducing the reflection of the illumination light by the cornea and the crystalline lens of the eye E to be inspected, a function of adjusting the brightness of the illumination light, and the like. The illumination light that has passed through the illumination diaphragm 33 is incident on the condensing lens 34.

The condensing lens 34 condenses the illumination light incident from the illumination diaphragm 33 on the visual field diaphragm 35.

The field diaphragm 35 has a translucent portion that transmits the illumination light incident from the condensing lens 34, and the size (aperture diameter) of the transmissive portion can be changed. By adjusting the diaphragm diameter, the visual field diaphragm 35 adjusts the irradiation field of the illumination light (gap light L1 or the like) output by the light source 31 with respect to the eye E to be inspected. The illumination light that has passed through the field diaphragm 35 is incident on the gap forming portion 36.

The narrow gap forming unit 36 generates a small gap light L1 from the illumination light incident from the field diaphragm 35, and emits the small gap light L1 toward the condensing lens 37. The gap forming portion 36 has a pair of slit blades, and the width of the gap light L1 is adjusted by changing the interval (slit width) between the slit blades. The gap forming portion 36 allows the illumination light from the light source 31 to pass as it is by widening the interval between the slit blades when observing the fluorescence of the eye E to be examined and when observing the meibomian glands, which will be described later.

The optical filter 38 is removably arranged in the optical path of the illumination system 18 between the gap forming portion 36 and the condensing lens 37. Examples of the optical filter 38 include a blue filter, a non-red filter, an ND (Neutral Density) filter, a color temperature change filter, an IR (Infrared) cut filter, and an IR transmission filter. An optical filter 38 other than these may be used. Further, a UV (ultraviolet) cut filter that cuts ultraviolet light contained in the illumination light L0 or the gap light L1 is constantly inserted in the optical path of the illumination system 18.

The blue filter is a filter used for observing the fluorescence of the eye E to be inspected to which a fluorescence contrast agent (fluorescein) has been administered, and transmits light in the blue wavelength range. The non-red filter is a filter used when inspecting abnormalities of optic nerve fibers, and is an optical filter (green filter or the like) that cuts light in the red wavelength range. The ND filter is an optical filter for changing (decreasing) the transmittance of the illumination light L0 or the gap light L1.

The color temperature conversion filter is an optical filter that lowers the color temperature of the illumination light L0 or the gap light L1 to convert it into warm color light. When this color temperature conversion filter is used, a cool white light source is used as the above-mentioned light source 31. The IR cut filter cuts infrared light contained in the illumination light L0 or the gap light L1. The IR transmission filter transmits infrared light. This IR transmission filter is used when illuminating the eye E to be inspected with infrared light (including near-infrared light) and observing the meibomian glands of the eye E to be inspected.

Each optical filter 38 is fitted in a filter turret 39 (see FIG. 3) in a state of being arranged in a direction around the axis about an axis parallel to the optical axis O1. Then, by rotating the filter turret 39 under the control of the control unit 20, each optical filter 38 is selectively inserted into the optical path of the illumination system 18. Further, by providing a plurality of filter turrets 39, a plurality of types of optical filters 38 can be simultaneously inserted into the optical path of the illumination system 18.

The condenser lens 37 collects the gap light L1 incident from the gap forming portion 36 or the illumination light incident from the optical filter 38 on the condenser lens 37.

The mirror 25 reflects (deflects) the gap light L1 or a part of the illumination light incident from the condensing lens 37 toward the eye E to be inspected. In addition, instead of the mirror 25, a prism or a beam splitter (including a half mirror, a dichroic mirror, and a polarizing beam splitter) may be used. Hereinafter, in order to prevent complication of the description, unless otherwise specified, it is assumed that the illumination system 18 irradiates the eye E to be inspected with the gap light L1.

<Structure of observation system and photography system>
The observation system 19 includes a pair of left and right optical systems such as a Galileo type or a Greeno type corresponding to both eyes of the eye E to be inspected. The left and right optical systems have almost the same configuration. The examiner visually observes the anterior segment of the eye E to be inspected by the left and right optical systems. Note that FIG. 2 shows only one of the left and right optical systems of the observation system 19.

The optical system of the observation system 19 includes an objective lens 41, a variable magnification optical system 42, an aperture 43, a barrier filter 44, a beam splitter 45, a relay lens 46, a prism 47, and an eyepiece lens 48.

The objective lens 41 emits the reflected light L2 from the eye E to be examined toward the variable magnification optical system 42.

For the variable magnification optical system 42, for example, a known drum type variable magnification mechanism is used. The variable magnification optical system 42 includes variable magnification lenses 42a and 42b. The variable magnification lenses 42a and 42b move along the optical axis O2 in response to the operation of the observation magnification operation knob 28 described above. As a result, the magnification (angle of view) of the anterior segment image 27 (also referred to as an observation image) of the anterior segment of the eye E to be inspected formed by the reflected light L2 can be changed in multiple steps. The reflected light L2 transmitted through the variable magnification optical system 42 is emitted toward the barrier filter 44 or the beam splitter 45.

As the variable magnification optical system 42, the magnification of the anterior segment image 27 is increased by electrically moving the variable magnification lenses 42a and 42b along the optical axis O2 using a switch or the like (not shown) and a lens driving unit. It may be adjustable in multiple stages.

A diaphragm 43 is arranged between the variable magnification lenses 42a and 42b. The diaphragm 43 has a translucent portion that transmits the reflected light L2 incident from the variable magnification lens 42a, and the size (aperture diameter) of the transmissive portion can be changed. The diaphragm 43 is an optical member that adjusts the amount of reflected light L2 incident on the observation eye Eo and the image pickup device 53 by adjusting the diaphragm diameter.

The barrier filter 44 is freely inserted and removed from the optical path of the observation system 19 between the variable magnification optical system 42 and the beam splitter 45. The barrier filter 44 is an optical filter that is inserted into the optical path of the reflected light L2 when observing the fluorescence of the eye E to be inspected, and is a bandpass that transmits a wavelength component corresponding to the fluorescence emitted by the fluorescent agent administered to the eye E to be inspected. It is an optical filter such as a filter. The barrier filter 44 is held by a filter driving unit 67 (see FIG. 3) described later, and is inserted and removed from the optical path of the observation system 19 under the control of the control unit 20.

The beam splitter 45 is provided on one or both of the left and right optical systems of the observation system 19. The beam splitter 45 splits the reflected light L2 incident from the variable magnification optical system 42 or the barrier filter 44 into two. Then, the beam splitter 45 emits one of the reflected light L2 divided into two toward the relay lens 46, and emits the other of the reflected light L2 toward the photographing system 29.

The relay lens 46 emits the reflected light L2 incident from the beam splitter 45 toward the prism 47.

The prism 47 includes two optical elements 47a and 47b, and translates the traveling direction of the reflected light L2 incident from the relay lens 46 upward in parallel, and images the reflected light L2 at the imaging position P.

The eyepiece lens 48 is provided in the eyepiece portion 24a. As a result, the observation eye Eo can observe the anterior segment image 27 (enlarged image thereof) of the eye E to be inspected formed by the reflected light L2 imaged at the imaging position P by the prism 47 through the eyepiece 48.

The photographing system 29 includes a relay lens 51, a mirror 52, and an image sensor 53. The relay lens 51 emits the reflected light L2 incident from the beam splitter 45 toward the mirror 52. The mirror 52 reflects the reflected light L2 incident from the relay lens 51 toward the image pickup device 53. The reflected light L2 reflected by the mirror 52 is imaged on the image pickup surface of the image pickup device 53 through an imaging lens (not shown).

As the image sensor 53, for example, a CMOS (complementary metal oxide semiconductor) type or CCD (Charge Coupled Device) type image sensor is used. The image sensor 53 captures the reflected light L2 imaged on the image pickup surface and outputs the captured image data 27D of the anterior segment image 27 to the control unit 20. The image pickup of the reflected light L2 by the image pickup element 53 is continuously executed at a predetermined frame rate, and the captured image data 27D (live image data of the anterior segment portion) is sequentially input from the image pickup element 53 to the control unit 20. .. When the operation switch (not shown) of the above-described operation lever 15 is pressed, the control unit 20 performs various image processing on the captured image data 27D input from the image sensor 53 and before the eye E to be inspected. Generates still image data of the eye.

<Function of control unit>
FIG. 3 is a functional block diagram of the control unit 20 of the first embodiment. As shown in FIG. 3, the control unit 20 includes an arithmetic circuit composed of various processors, memories, and the like. 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 FPGA (Field Programmable Gate Arrays)] and the like. The various functions of the control unit 20 may be realized by one processor, or may be realized by a plurality of processors of the same type or different types.

The control unit 20 operates the operation of each part of the slit lamp microscope 10 in response to the operation of the operation unit 68 by the examiner, specifically, the electric drive unit 13, the lighting system 18, the observation system 19, the photographing system 29, and the like. Control the operation. Further, although the details will be described later, the control unit 20 estimates (measures) the irradiation light amount of the gap light L1 with respect to the eye subject E in order to protect the eye subject E from optical hazards, and the irradiation light amount is predetermined. When it becomes larger than the upper limit value, the warning information 94 (see FIG. 9) is notified to the examiner via the display unit 62A and the speaker 62B described later.

In addition to the electric drive unit 13, the light source 31, and the image sensor 53 described above, the control unit 20 includes a storage unit 61, a display unit 62A, a speaker 62B, an illumination diaphragm drive unit 63, a field diaphragm drive unit 64, and a slit drive. A unit 65, a filter drive unit 66, a filter drive unit 67, an operation unit 68, a detection unit 70, and the like are connected. In the drawing, the position adjusting unit for adjusting the positions of the chin rest 12a and the forehead pad 12b and the diaphragm driving unit for adjusting the diaphragm diameter of the diaphragm 43 in the observation system 19 are not shown.

The storage unit 61 executes the operation control of the electric drive unit 13, the lighting system 18, the observation system 19, the photographing system 29, etc., and the notification control of the optical hazard warning information 94 (see FIG. 9) to the control unit 20. It stores a control program (not shown) for making it. In addition, various information such as still image data of the anterior segment of the eye E to be inspected described above is also stored in the storage unit 61.

The display unit 62A is a known monitor such as a liquid crystal display (a touch panel type liquid crystal display is also possible), and is provided on the surface of the housing of the slit lamp microscope 10 or outside the housing. The display unit 62A displays various information under the control of the control unit 20. For example, the display unit 62A displays an operation screen for operating each part of the slit lamp microscope 10 and displays an image based on the above-mentioned captured image data 27D (live image, still image). The display unit 62A also displays the optical hazard warning information 94 (see FIG. 9).

The speaker 62B is provided on the surface of the housing of the slit lamp microscope 10 or outside the housing. The speaker 62B outputs various information by voice under the control of the control unit 20. Further, the speaker 62B outputs the warning information 94 (see FIG. 9) of the optical hazard by voice.

Each drive unit such as the illumination diaphragm drive unit 63, the field diaphragm drive unit 64, the slit drive unit 65, the filter drive unit 66, and the filter drive unit 67 includes, for example, various actuators (not shown) and the driving force of the actuators. (Not shown) and a transmission mechanism (not shown).

The illumination diaphragm drive unit 63 drives the illumination diaphragm 33 to adjust the aperture diameter. The field diaphragm drive unit 64 drives the field diaphragm 35 to adjust the diaphragm diameter. The slit drive unit 65 adjusts the distance between the pair of slit blades of the gap forming portion 36, that is, the width of the gap light L1.

The filter driving unit 66 rotationally drives the above-mentioned filter turret 39 to selectively insert each optical filter 38 into the optical path of the illumination system 18. The filter driving unit 67 inserts and removes the barrier filter 44 from the optical path of the observation system 19 by moving the barrier filter 44 in the direction perpendicular to the optical axis O2.

The operation unit 68 is used for operating each part of the slit lamp microscope 10. The operation unit 68 includes a hand operation unit 72 in addition to the operation lever 15 and the observation magnification operation knob 28 described above. The configuration for operating the jaw cradle 12 and the diaphragm 43 is not shown.

The operating lever 15 is provided with a linear-acting potentiometer (not shown), and the linear-acting potentiometer detects tilting operations of the operating lever 15 in the front-rear direction and the left-right direction. The control unit 20 drives the electric drive unit 13 to move the moving stage 14 in the front-rear direction or the left-right direction based on the detection result of the direct-acting potentiometer.

The observation magnification operation knob 28 is used for a magnification selection operation for selecting the magnification of the anterior segment image 27. In response to this magnification selection operation, the variable magnification optical system 42 changes the magnification of the anterior segment image 27.

The hand operation unit 72 is a physical operation member such as a switch, a lever, a handle, and a key, or a virtual operation input unit such as an icon in an operation screen displayed on the display unit 62A. The hand operation unit 72 has two diaphragm diameter selection operations for selecting the respective diaphragm diameters of the illumination diaphragm 33 and the field diaphragm 35, and the distance between the pair of slit blades of the gap forming portion 36 (width of the gap light L1). It is used for an interval adjusting operation for adjusting, a filter selection operation for selecting an optical filter 38 to be inserted into the optical path of the illumination system 18, and a filter insertion / removal operation for selecting the insertion / removal of the barrier filter 44.

The control unit 20 drives the illumination aperture drive unit 63 to adjust the aperture diameter of the illumination aperture 33, or drives the field aperture drive unit 64 to view the field in response to each aperture diameter selection operation by the hand operation unit 72. The aperture diameter of the aperture 35 is adjusted. Further, the control unit 20 drives the slit drive unit 65 to adjust the distance between the pair of slit blades in response to the interval adjustment operation by the hand operation unit 72. Further, the control unit 20 drives the filter drive unit 66 to rotate the filter turret 39 in response to the filter selection operation by the hand operation unit 72. Furthermore, the control unit 20 drives the filter drive unit 67 to perform the insertion / removal of the barrier filter 44 with respect to the optical path of the observation system 19 in response to the filter insertion / removal operation of the hand operation unit 72.

The detection unit 70 is used for measuring the integrated irradiation time of the gap light L1 on the eye E to be inspected by the irradiation time measuring unit 82 described later. Examples of the detection unit 70 include the following first to third examples.

FIG. 4 is an explanatory diagram for explaining a first example of the detection unit 70. As shown in FIG. 4, the detection unit 70 of the first example (corresponding to the operation detection unit of the present invention) turns on / off the light source 31 based on, for example, a signal from the light source 31 or a power source (not shown) of the light source 31. It is a detection sensor that detects. The detection unit 70 of the first example may be provided in the light source 31. The detection unit 70 of the first example continuously (continuously) detects the on / off of the light source 31, and continuously outputs the detection result to the irradiation time measurement unit 82. In addition, "continuous" in the present specification includes "indefinite interval" in addition to "constant interval".

FIG. 5 is an explanatory diagram for explaining a second example of the detection unit 70. As shown in FIG. 5, the detection unit 70 of the second example (corresponding to the position detection unit of the present invention) is the position of the lighting system 18 or the like which is horizontally moved by the electric drive unit 13 via the moving stage 14 or the like. It is a known position detection sensor such as a linear scale that detects. Based on the detection result of the detection unit 70 of the second example, for example, the working distance WD (work distance) between the eye E to be inspected and the illumination system 18 and the like is assumed when observing the eye E to be inspected by the slit lamp microscope 10. It is possible to confirm whether or not it is within a certain range. Then, the detection unit 70 of the second example continuously detects the position of the illumination system 18 and the like, and continuously outputs the detection result to the irradiation time measurement unit 82.

FIG. 6 is an explanatory diagram for explaining a third example of the detection unit 70. As shown in FIG. 6, the detection unit 70 of the third example (corresponding to the face detection unit of the present invention) is, for example, a contact type or non-contact type detection sensor provided on the chin receiver 12a, and the chin receiver 12a Detects the presence or absence of support of the subject's face. The detection unit 70 of the third example continuously detects the presence or absence of support of the subject's face by the chin support 12a, and continuously outputs the detection result to the irradiation time measurement unit 82.

Returning to FIG. 3, the control unit 20 executes a control program (not shown) in the storage unit 61 to execute the drive condition acquisition unit 80, the irradiation time measurement unit 82, the irradiation light amount estimation unit 84, and the first notification control unit. It functions as 86 and a second notification control unit 88. Note that, among the various functions of the control unit 20, only the function related to the notification of the optical hazard warning information 94 (see FIG. 9) is shown in FIG. 3, and the other functions are shown because they are known techniques. Is omitted.

The drive condition acquisition unit 80, the irradiation time measurement unit 82, the irradiation light amount estimation unit 84, the first notification control unit 86, and the second notification control unit 88 of the control unit 20 are input by, for example, to the operation unit 68 by the examiner. It operates according to a predetermined start operation (a power-on operation of the slit lamp microscope 10 is also possible). In this case, the examiner inputs a start operation to the operation unit 68 for each eye E on the left and right of the examinee.

The drive condition acquisition unit 80 acquires the drive conditions of the light source 31. The drive condition of the light source 31 is a drive condition related to the intensity of the illumination light emitted from the light source 31, that is, a drive condition related to the intensity of the gap light L1 emitted from the illumination system 18 to the eye E to be inspected. As described above, the intensity here is the amount of light per unit time in a unit area (for example, J · cm ^-2 · s ^-1 ), and is also referred to as irradiance.

The drive condition of the light source 31 is, for example, a drive voltage value of the light source 31 when the light source 31 is a halogen lamp, and a drive current value of the light source 31 when the light source 31 is an LED light source. Therefore, the drive condition acquisition unit 80 acquires the drive voltage value or the drive current value as the drive condition of the light source 31 via a detection circuit (not shown) that measures the drive voltage value or the drive current value of the light source 31. Then, when the intensity of the illumination light emitted from the light source 31 is fixed, the drive condition acquisition unit 80 acquires the drive condition of the light source 31 once at a predetermined timing (for example, at startup) to drive the light source 31. The acquisition result of the condition is output to the irradiation light amount estimation unit 84. Further, when the intensity of the illumination light emitted from the light source 31 (that is, the driving condition of the light source 31) is variable, the drive condition acquisition unit 80 obtains the driving condition at least every time the driving condition of the light source 31 is changed. The acquisition of the driving conditions is repeated, and the acquisition results of the driving conditions are sequentially output to the irradiation light amount estimation unit 84. In this case, the drive condition acquisition unit 80 may acquire the above-mentioned continuous (regular interval, irregular interval) drive condition.

The irradiation time measuring unit 82 continuously measures the integrated irradiation time of the gap light L1 on the eye E to be inspected based on the detection result of the detection unit 70 of any of the examples shown in FIGS. 4 to 6 described above. To do.

As shown in FIG. 4 described above, when the irradiation time measuring unit 82 continuously acquires the detection result of the detection unit 70 of the first example, the time during which the light source 31 is turned on based on this detection result. Is continuously measured (counted) as the integrated irradiation time of the gap light L1. This prevents the time when the light source 31 is turned off, that is, the time when the gap light L1 is not actually irradiated to the eye E to be inspected is counted as the integrated irradiation time.

As shown in FIG. 5 described above, when the irradiation time measuring unit 82 continuously acquires the detection result of the detection unit 70 of the second example, the position of the illumination system 18 is determined based on the position detection result. It is continuously determined whether or not it is set within the predetermined irradiation position range. This irradiation position range is determined based on, for example, the assumed range of the working distance WD described above in the front-back direction in the horizontal direction, and is determined based on the position range of the jaw cradle 12 in the left-right direction in the horizontal direction. That is, the irradiation position range is the position range of the illumination system 18 such that the illumination system 18 is roughly aligned with the eye E to be inspected in the horizontal direction.

Then, the irradiation time measuring unit 82 continuously measures the time when the position of the illumination system 18 is set within the above-mentioned irradiation position range as the integrated irradiation time of the gap light L1. As a result, the time during which the illumination system 18 and the eye E to be inspected are largely displaced in the horizontal direction regardless of whether the light source 31 is turned on or off, that is, the time when the eye E is not actually irradiated with the gap light L1. Is prevented from being counted in the integrated irradiation time.

As shown in FIG. 6 described above, when the irradiation time measuring unit 82 continuously acquires the detection result of the detection unit 70 of the third example, the jaw receiver 12a of the subject is based on the detection result. The time for supporting the face is continuously measured as the integrated irradiation time of the gap light L1. As a result, the integrated irradiation time is the time when the subject's face is not supported by the jaw receiver 12a regardless of whether the light source 31 is on or off, that is, the time when the gap light L1 is not actually irradiated to the eye E to be examined. It is prevented from counting to.

Returning to FIG. 3, the irradiation time measuring unit 82 continuously measures the integrated irradiation time of the gap light L1 with respect to the eye E to be inspected, and sequentially outputs the measurement result to the irradiation light amount estimation unit 84. The irradiation time measuring unit 82 may continuously measure the integrated irradiation time of the gap light L1 based on the result of combining two or more of the detection results of the detection units 70 of each example. As a result, the integrated irradiation time can be measured with higher accuracy than when the integrated irradiation time is measured based on the independent detection result of the detection unit 70 of each example.

FIG. 7 is an explanatory diagram for explaining the estimation of the irradiation light amount of the gap light L1 by the irradiation light amount estimation unit 84. As shown in FIG. 7 and FIG. 3 described above, the irradiation light amount estimation unit 84 receives the drive condition (drive voltage value or drive current value) of the light source 31 that is input once or repeatedly from the drive condition acquisition unit 80, and the irradiation. Based on the integrated irradiation time continuously input from the time measuring unit 82, the irradiation light amount of the gap light L1 to be irradiated to the eye E to be inspected is continuously estimated. The irradiation light amount referred to here is a physical quantity obtained by time-integrating the intensity of light as described above, in other words, the irradiation light amount per unit area (for example, Jcm- ² ).

First, the irradiation light amount estimation unit 84 determines the intensity of the gap light L1 irradiated to the eye E to be inspected based on the drive condition (drive voltage value or drive current value) of the light source 31 input from the drive condition acquisition unit 80. Estimate (measure). Corresponding information 90 in the storage unit 61 is used for this estimation. The correspondence information 90 stores the correspondence between the driving conditions corresponding to the type of the light source 31 and the gap light L1 irradiated to the eye E to be inspected, and is obtained by an experiment, a simulation, or the like. As a result, the irradiation light amount estimation unit 84 estimates the intensity of the gap light L1 by referring to the corresponding information 90 in the storage unit 61 based on the drive condition of the light source 31 input from the drive condition acquisition unit 80. be able to.

When the drive condition is repeatedly input from the drive condition acquisition unit 80, the irradiation light amount estimation unit 84 repeatedly estimates the intensity of the gap light L1 each time a new drive condition is input.

Next, the irradiation light amount estimation unit 84 time-integrates the intensity of the gap light L1 estimated from the driving conditions based on the integrated irradiation time input from the irradiation time measurement unit 82, thereby causing the gap light to the eye E to be inspected. The amount of irradiation light of L1 is estimated. Then, the irradiation light amount estimation unit 84 receives the irradiation light amount based on the driving condition of the light source 31 input once or repeatedly from the driving condition acquisition unit 80 and the integrated irradiation time continuously input from the irradiation time measuring unit 82. The irradiation light amount of the gap light L1 irradiated to the eye examination E is continuously estimated, and a new estimation result is sequentially output to both the first notification control unit 86 and the second notification control unit 88.

FIG. 8 is an explanatory diagram for explaining the notification of the irradiation light amount of the gap light L1. As shown in FIG. 8, the first notification control unit 86 constitutes the irradiation light amount notification unit of the present invention together with the display unit 62A and the speaker 62B described above. Based on the estimation result of the irradiation light amount input from the irradiation light amount estimation unit 84, the first notification control unit 86 displays the irradiation light amount information 92 indicating the irradiation light amount on the display unit 62A and outputs the sound from the speaker 62B. Then, the first notification control unit 86 displays the latest irradiation light amount information 92 on the display unit 62A and the speaker each time the estimation result of the irradiation light amount of the new gap light L1 is input from the irradiation light amount estimation unit 84. Audio is output from 62B. As a result, the examiner can recognize the latest irradiation light amount of the gap light L1 with respect to the eye E to be inspected.

FIG. 9 is an explanatory diagram for explaining the notification of the warning information 94 of the optical hazard. As shown in FIG. 9, the second notification control unit 88 constitutes the warning information notification unit of the present invention together with the display unit 62A and the speaker 62B described above. The second notification control unit 88 determines whether or not the irradiation light amount becomes larger than a predetermined upper limit value each time a new irradiation light amount estimation result is continuously input from the irradiation light amount estimation unit 84. judge. This upper limit is set in advance based on the ISO standard described above in order to protect the eye E to be inspected from optical hazards, and is, for example, a value smaller than the maximum allowable amount of irradiation light by a predetermined margin. is there.

Then, when the irradiation light amount of the gap light L1 becomes larger than the upper limit value, the second notification control unit 88 displays the warning information 94 (caution information) of the optical hazard on the display unit 62A and from the speaker 62B. Output audio. As a result, the warning information 94 can be notified to the examiner using the display unit 62A and the speaker 62B. By outputting the warning information 94 by voice from the speaker 62B, the warning information 94 is reliably provided to the examiner even when the observer's observation eye Eo is observing the anterior eye portion image 27 through the eyepiece 24a. Can be notified to.

[Action of slit lamp microscope]
FIG. 10 is a flowchart showing the flow of estimating the irradiation light amount of the slit light L1 by the slit lamp microscope 10 having the above configuration and notifying the warning information 94 of the optical hazard (corresponding to the operation method of the ophthalmic apparatus of the present invention). ..

As shown in FIG. 10, when the examiner inputs a predetermined start operation to the operation unit 68 when observing the eye E to be inspected using the slit lamp microscope 10 (step S1), the control unit 20 displays. It functions as a drive condition acquisition unit 80, an irradiation time measurement unit 82, an irradiation light amount estimation unit 84, a first notification control unit 86, and a second notification control unit 88.

Next, the drive condition acquisition unit 80 acquires the drive condition (drive voltage value or drive current value) of the light source 31 corresponding to the type of the light source 31 and outputs this drive condition to the irradiation light amount estimation unit 84 (step S2). , Corresponding to the driving condition acquisition step of the present invention).

On the other hand, at the same time as or before or after the acquisition of the drive condition by the drive condition acquisition unit 80, the irradiation time measurement unit 82 obtains the detection result from the detection unit 70 of any of the above-described examples 4 to 6. Obtained (step S3), and based on this detection result, the integrated irradiation time of the gap light L1 on the eye E to be inspected is measured (step S4, corresponding to the integrated irradiation time measurement step of the present invention). As a result, the time when the light source 31 is turned on, the time when the position of the lighting system 18 is set within the above-mentioned irradiation position range, or the time when the subject's face is supported by the chin rest 12a It is the integrated irradiation time. As a result, it is possible to prevent the time when the interstitial light L1 is not irradiated to the eye E to be counted as the integrated irradiation time, so that the integrated irradiation time can be accurately measured. Then, the irradiation time measuring unit 82 outputs the measurement result of the integrated irradiation time to the irradiation light amount estimation unit 84.

Upon receiving the input of the driving conditions and the measurement results of the integrated irradiation time, the irradiation light amount estimation unit 84 starts estimating the irradiation light amount of the gap light L1 irradiated to the eye E to be inspected. First, as shown in FIG. 7, the irradiation light amount estimation unit 84 stores the storage unit 61 based on the drive conditions (drive voltage value or drive current value) of the light source 31 input from the drive condition acquisition unit 80. With reference to the corresponding information 90 in the above, the intensity of the gap light L1 irradiated to the eye E to be inspected is estimated.

Next, the irradiation light amount estimation unit 84 determines the irradiation light amount of the gap light L1 to the eye E to be inspected based on the intensity of the gap light L1 estimated from the driving conditions and the integrated irradiation time input from the irradiation time measuring unit 82. Is estimated, and the estimation result of the irradiation light amount is output to the first notification control unit 86 and the second notification control unit 88, respectively (step S5, corresponding to the irradiation light amount estimation step of the present invention).

Upon receiving the input of the estimation result of the irradiation light amount of the narrow gap light L1, the first notification control unit 86 displays the irradiation light amount information 92 indicating the irradiation light amount on the display unit 62A and outputs the sound from the speaker 62B (step S6). .. As a result, the display unit 62A and the speaker 62B notify the examiner of the irradiation light amount information 92.

In addition, the second notification control unit 88 that receives the input of the estimation result of the irradiation light amount of the gap light L1 determines whether or not the irradiation light amount becomes larger than the above-mentioned upper limit value (step S7). Then, the second notification control unit 88 goes into a standby state when the irradiation light amount is equal to or less than the upper limit value (NO in step S7).

On the other hand, when the irradiation light amount is larger than the upper limit value, the second notification control unit 88 displays the warning information 94 of the optical hazard on the display unit 62A and outputs the sound from the speaker 62B (YES in step S7, step S8). , Corresponding to the warning information notification step of the present invention). As a result, the warning information 94 is notified to the examiner from the display unit 62A and the speaker 62B.

Hereinafter, the above-described processes from step S1 to step S8 are repeatedly executed until the observation of the eye E to be inspected using the slit lamp microscope 10 is completed (step S9). As a result, acquisition of driving conditions, measurement of integrated irradiation time, estimation and notification of irradiation light amount are continuously executed, and when the irradiation light amount becomes larger than the upper limit value, warning information 94 is notified to the examiner. Is executed. The second and subsequent acquisition of the driving conditions in step S2 may be executed according to the change in the driving conditions of the light source 31. Further, when the intensity of the illumination light emitted from the light source 31 is fixed, the driving condition in step S2 may be acquired only once.

[Effect of this embodiment]
As described above, in the present embodiment, in addition to the intensity of the gap light L1 (illumination light) irradiated to the eye E to be examined, the integrated irradiation time of the gap light L1 irradiated to the eye E to be examined is taken into consideration. Since the irradiation light amount of the gap light L1 with respect to the eye examination E is estimated, this irradiation light amount can be obtained more accurately than before. As a result, the eye E to be inspected can be more reliably protected from optical hazards.

[Second Embodiment]
FIG. 11 is a functional block diagram of the control unit 20 of the slit lamp microscope 10 of the second embodiment. In addition, in FIG. 11 and later, the configuration which is not directly related to the protection of the optical hazard is not shown as appropriate. The irradiation time measuring unit 82 of the first embodiment measures the integrated irradiation time of the gap light L1 based on the detection result of the detection unit 70 of each example, but the irradiation time measuring unit 82 of the second embodiment , The integrated irradiation time of the gap light L1 is measured based on the analysis result of the photographed image data 27D continuously input from the image sensor 53 of the photographing system 29.

As shown in FIG. 11, in the slit lamp microscope 10 of the second embodiment, the control unit 20 functions as a light irradiation detection unit 100 in addition to each unit of the first embodiment, and the slit light by the irradiation time measurement unit 82 The configuration is basically the same as that of the first embodiment, except that the method of measuring the integrated irradiation time of L1 is different. Therefore, those having the same function or configuration as the first embodiment are designated by the same reference numerals and the description thereof will be omitted.

FIG. 12 is an explanatory diagram for explaining the function of the light irradiation detection unit 100. As shown in reference numeral XIIA of FIG. 12 and FIG. 11 described above, the light irradiation detection unit 100 performs image analysis for each photographed image data 27D continuously input from the image sensor 53, and is in front of the eye E to be inspected. It is detected whether or not the interstitial light L1 is irradiated to the eye portion. Specifically, in the light irradiation detection unit 100, for each captured image data 27D, an optical image 102 showing the gap light L1 irradiated to the anterior segment of the eye E to be inspected is an anterior segment image based on the captured image data 27D. Detects whether or not it is contained in 27.

Here, a method of detecting (extracting) the anterior segment image 27 from the captured image data 27D is a known technique. Further, the pixel values of the pixels constituting the optical image 102 are higher than the pixel values of the other pixels of the captured image data 27D. Therefore, among the pixels constituting the anterior segment image 27 of the captured image data 27D, the pixels whose pixel values are equal to or higher than a predetermined threshold value can be identified as the pixels of the optical image 102. Therefore, each time the light irradiation detection unit 100 inputs new captured image data 27D from the image pickup element 53, the light irradiation detection unit 100 analyzes the captured image data 27D to include the optical image 102 in the anterior eye portion image 27. It is possible to detect whether or not the gap light L1 is irradiated to the anterior segment of the eye E to be inspected.

According to the above-mentioned detection method of the optical image 102, as shown by the reference numeral XIIB in FIG. 12, the optical image 102 is included in the anterior segment image 27 regardless of the shape of the light applied to the eye E to be inspected. It is possible to detect whether or not it is. That is, it is possible to detect whether or not the anterior segment of the eye E to be inspected is irradiated with various illumination lights other than the gap light L1.

In this way, each time the light irradiation detection unit 100 inputs new captured image data 27D from the image pickup element 53, the presence or absence of the optical image 102 in the anterior eye portion image 27 based on the captured image data 27D (of the eye to be inspected E The presence or absence of irradiation of the interstitial light L1 to the anterior segment of the eye) is detected, and the detection result is sequentially output to the irradiation time measuring unit 82.

FIG. 13 is an explanatory diagram for explaining the measurement of the integrated irradiation time of the gap light L1 by the irradiation time measuring unit 82 of the second embodiment. As shown in FIG. 13 and FIG. 11 described above, the irradiation time measuring unit 82 of the second embodiment is based on the detection results for each of the captured image data 27D sequentially input from the light irradiation detecting unit 100, and the gap light L1 The integrated irradiation time of is continuously measured.

For example, the irradiation time measuring unit 82 includes the number of captured image data 27D (photographed image data 27D of the anterior segment irradiated with the gap light L1) including the optical image 102, and a known frame of the image sensor 53. The integrated irradiation time of the gap light L1 is calculated based on the rate. Further, for example, when the captured image data 27D includes information on the imaging time, the irradiation time measuring unit 82 determines the gap light based on the imaging time of the captured image data 27D including the optical image 102. The integrated irradiation time of L1 is calculated.

Hereinafter, the irradiation time measuring unit 82 repeatedly executes the calculation of the integrated irradiation time of the gap light L1 each time the detection result from the light irradiation detecting unit 100 is input. As a result, the integrated irradiation time is continuously measured by the irradiation time measuring unit 82 as in the first embodiment. Then, each time the irradiation time measuring unit 82 calculates the integrated irradiation time of the gap light L1, a new calculation result is output to the irradiation light amount estimation unit 84 as the measurement result of the integrated irradiation time.

The other processes (acquisition of driving conditions, estimation of the irradiation light amount of the gap light L1, notification of the irradiation light amount information 92, and notification of the warning information 94) are the same as those in the first embodiment. Omit.

As described above, in the second embodiment, the integrated irradiation time of the gap light L1 is measured based on the analysis result of the captured image data 27D continuously input from the image sensor 53 of the photographing system 29, so that the eye E is examined. On the other hand, it is possible to more reliably prevent the time when the gap light L1 is not irradiated from being counted as the integrated irradiation time as compared with the first embodiment. As a result, the integrated irradiation time can be measured with higher accuracy than that of the first embodiment.

[Third Embodiment]
FIG. 14 is a functional block diagram of the control unit 20 of the slit lamp microscope 10 of the third embodiment. FIG. 15 is an explanatory diagram showing an example of the integrated map image 106 generated by the control unit 20 of the third embodiment. In the second embodiment, the integrated irradiation time of the gap light L1 is measured based on the analysis result of each captured image data 27D, but in the third embodiment, the front is measured based on the analysis result of each captured image data 27D. An integrated map image 106 showing the amount of irradiation light of the gap light L1 for each of the plurality of regions 27R of the eye image 27 is generated.

As shown in FIGS. 14 and 15, in the slit lamp microscope 10 of the third embodiment, the control unit 20 functions as an irradiation position detection unit 104 in addition to each unit of the second embodiment and generates an integrated map image 106. The configuration is basically the same as that of the second embodiment except for the above-mentioned points. Therefore, those having the same function or configuration as each of the above embodiments are designated by the same reference numerals and the description thereof will be omitted.

The light irradiation detection unit 100 of the third embodiment sequentially outputs the detection result of the presence / absence of the light image 102 for each captured image data 27D to the irradiation position detection unit 104.

The irradiation position detection unit 104 is based on the detection result of the light irradiation detection unit 100, and for each photographed image data 27D of the anterior segment of the eye to be inspected E irradiated with the gap light L1, the anterior eye based on the captured image data 27D. The irradiation position of the gap light L1 in the part image 27 is detected.

Specifically, the irradiation position detection unit 104 places the optical image 102 in the anterior eye portion image 27 based on the detection result of the presence or absence of the optical image 102 for each captured image data 27D sequentially input from the light irradiation detection unit 100. The position of the optical image 102 in the anterior segment image 27 is sequentially detected for each captured image data 27D including the captured image data 27D (hereinafter referred to as specific captured image data 27D). Here, the position of the optical image 102 in the anterior segment image 27 is, for example, the position coordinates in the captured image data 27D of each pixel constituting the optical image 102, and is fine in the anterior segment image 27. It corresponds to the irradiation position of the gap light L1. Then, the irradiation position detection unit 104 sequentially outputs the position detection result of the optical image 102 for each specific captured image data 27D to the irradiation time measurement unit 82.

The irradiation time measuring unit 82 of the third embodiment divides the anterior segment image 27 into a plurality of regions based on the position detection result for each specific captured image data 27D sequentially input from the irradiation position detecting unit 104. The integrated irradiation time of the gap light L1 is measured (calculated) over time for each 27R. The size of each region 27R is not particularly limited, and each region 27R may be composed of one pixel or may be composed of a plurality of pixels.

The integrated irradiation time of the gap light L1 for each region 27R can be obtained by individually executing the calculation of the integrated irradiation time of the gap light L1 described in the second embodiment above for each region 27R. Hereinafter, the irradiation time measuring unit 82 repeatedly executes the calculation of the integrated irradiation time of the gap light L1 for each region 27R every time a new position detection result is input from the irradiation position detecting unit 104. As a result, the irradiation time measuring unit 82 continuously measures the integrated irradiation time for each region 27R. Then, each time the irradiation time measuring unit 82 calculates the integrated irradiation time of the gap light L1 for each region 27R, a new calculation result is sent to the irradiation light amount estimation unit 84 as a measurement result of the integrated irradiation time for each region 27R. Output sequentially.

The irradiation light amount estimation unit 84 of the third embodiment includes the measurement result of the integrated irradiation time of the gap light L1 for each region 27R sequentially input from the irradiation time measurement unit 82, and the light source 31 input from the drive condition acquisition unit 80. The irradiation light amount of the gap light L1 for each region 27R is continuously estimated based on the driving condition of the above and the corresponding information 90 in the storage unit 61. The amount of irradiation light of the gap light L1 for each region 27R can be obtained by executing the calculation of the amount of irradiation light for the gap light L1 described in the first embodiment above for each region 27R. Then, each time the irradiation light amount estimation unit 84 estimates the irradiation light amount of the gap light L1 for each region 27R, a new estimation result is sequentially output to the first notification control unit 86 and the second notification control unit 88.

The first notification control unit 86 of the third embodiment receives the latest gap light L1 for each region 27R each time the estimation result of the irradiation light amount of the gap light L1 for each region 27R is input from the irradiation light amount estimation unit 84. An integrated map image 106 showing the amount of irradiation light of the above is generated, and the integrated map image 106 is superimposed and displayed on the anterior segment image 27 displayed on the display unit 62A. As a result, the integrated map image 106 displayed on the display unit 62A is sequentially updated. As a result, the examiner can grasp the amount of irradiation light for each region 27R of the anterior segment of the eye E to be inspected in real time.

In the integrated map image 106 shown in FIG. 15, the magnitude of the irradiation light amount of the gap light L1 for each region 27R is expressed by the shade (color distribution) of the image, but the gap light L1 for each region 27R is represented. The display mode of the integrated map image 106 is not particularly limited as long as the magnitude of the irradiation light amount can be discriminated.

The second notification control unit 88 of the third embodiment irradiates the gap light L1 for each region 27R based on the estimation result of the irradiation light amount of the gap light L1 for each region 27R sequentially input from the irradiation light amount estimation unit 84. It is determined whether or not the amount of light becomes larger than a predetermined upper limit value. Then, when the irradiation light amount of the gap light L1 becomes larger than the upper limit value in any one of the respective regions 27R, the second notification control unit 88 receives the optical hazard warning information 94 as in each of the above embodiments. Is displayed on the display unit 62A and the sound is output from the speaker 62B.

As described above, in the third embodiment, since the irradiation light amount of the gap light L1 can be estimated for each region 27R of the anterior segment of the eye E to be inspected, the examiner can estimate the irradiation light amount for each region 27R (that is, the irradiation light amount). Distribution) can be easily grasped. As a result, the entire region 27R of the anterior segment of the eye E to be inspected can be more reliably protected from optical hazards.

[Fourth Embodiment]
FIG. 16 is a functional block diagram of the control unit 20 of the slit lamp microscope 10 of the fourth embodiment. In each of the above embodiments, the illumination system 18 irradiates the eye E to be inspected with the gap light L1 (white light). However, as described above, the illumination system 18 rotates the filter turret 39 to rotate each optical filter. By selectively inserting the 38 into the optical path of the illumination system 18, various types of light can be applied to the eye E to be inspected.

For example, the illumination system 18 irradiates the eye E with blue light (excitation light) by inserting a blue filter into the optical path of the illumination light when observing the fluorescence of the eye E, and observes the mybome gland of the eye E. Occasionally, an IR transmission filter is inserted into the optical path of the illumination light to irradiate the eye E with infrared light. Therefore, the illumination system 18 selectively irradiates the eye E to be inspected with light in a plurality of wavelength ranges different from each other.

At this time, since the energy of the blue light on the low wavelength region side is higher than the energy of the infrared light on the long wavelength region side, the eye E to be inspected was irradiated with the same amount of blue light and infrared light. Even so, the effect on the eye E to be examined is greater in blue light than in infrared light. Therefore, in order to protect the eye E to be inspected from optical hazards, it is necessary to estimate the amount of irradiation light and notify the warning information 94 in consideration of the wavelength range of the light emitted from the illumination system 18 to the eye E to be inspected. preferable.

Therefore, as shown in FIG. 16, in the fourth embodiment, the irradiation light amount is estimated and the warning information 94 is notified in consideration of the wavelength range of the light emitted from the illumination system 18 to the eye E to be inspected. In the slit lamp microscope 10 of the fourth embodiment, the control unit 20 functions as a wavelength range detection unit 110 and a multiplication unit 112 in addition to the above-mentioned units, and the coefficient information 114 is stored in the storage unit 61. Except for the above points, the configuration is basically the same as that of each of the above embodiments. Therefore, those having the same function or configuration as each of the above embodiments are designated by the same reference numerals and the description thereof will be omitted.

The wavelength range detection unit 110 detects the wavelength range of the light emitted from the illumination system 18 to the eye E to be inspected. For example, the wavelength range detection unit 110 is irradiated to the eye E to be inspected by acquiring the setting information, that is, the information regarding the type of the optical filter 38 inserted in the optical path of the illumination system 18 from the filter turret 39. Detects the wavelength range of light.

Further, the colors of the anterior segment image 27 and its background image based on the above-mentioned captured image data 27D change according to the wavelength range of the light emitted to the eye E to be inspected. For example, the anterior segment image 27 and its background image become a green image during fluorescence observation, and the anterior segment image 27 and its background image become a monochrome image during infrared light observation. Therefore, the wavelength range detection unit 110 detects the wavelength range of the light emitted from the illumination system 18 to the eye E to be inspected by performing image analysis (color analysis) on the captured image data 27D sequentially output from the image sensor 53. can do.

Then, the wavelength range detection unit 110 continuously detects the wavelength range of the light emitted from the illumination system 18 to the eye E to be inspected, and sequentially outputs the detection result to the multiplication unit 112.

The drive condition acquisition unit 80 and the irradiation time measurement unit 82 of the fourth embodiment are basically the same as those of each of the above embodiments. When the integrated irradiation time is measured by the method described in the second embodiment and the third embodiment, the light irradiation detection unit 100 described above sets the captured image data 27D for each captured image data 27D. Image analysis (color analysis, etc.) is performed to detect the presence or absence of light irradiation on the anterior segment of the eye E to be inspected. As a result, the irradiation time measuring unit 82 can obtain the integrated irradiation time as in the second embodiment and the third embodiment.

The irradiation light amount estimation unit 84 of the fourth embodiment continuously estimates the irradiation light amount of various lights irradiated to the eye E to be inspected by the same method as in each of the above embodiments, and multiplies the estimation result of the irradiation light amount. It is sequentially output to 112.

Each time the multiplication unit 112 inputs a new estimation result of the irradiation light amount of the light to the eye E from the irradiation light amount estimation unit 84, the multiplication unit 112 has a coefficient () corresponding to the wavelength range of the light with respect to the irradiation light amount of the light. The so-called weighting is performed by multiplying (also called a weighting function).

First, the multiplication unit 112 determines a coefficient corresponding to the wavelength range of the light irradiating the eye E to be inspected. The coefficient information 114 in the storage unit 61 is used for this determination. The coefficient information 114 stores the correspondence between the wavelength range of the light irradiated to the eye E to be examined and the coefficient for multiplying the irradiation light amount of the light estimated by the irradiation light amount estimation unit 84. For example, the ISO described above is stored in the coefficient information 114. It is predetermined based on the standard and the like. As a result, the multiplication unit 112 irradiates the eye E to be inspected by referring to the coefficient information 114 in the storage unit 61 each time a detection result of the wavelength region of light is newly input from the wavelength region detection unit 110. It is possible to determine the coefficient corresponding to the wavelength range of the light.

Next, the multiplication unit 112 multiplies the determined coefficient by the irradiation light amount of the light newly input from the irradiation light amount estimation unit 84, and the irradiation light amount after the multiplication is the first notification control unit 86 and the second notification control unit 88. Output to both. Hereinafter, the multiplication unit 112 will be based on the detection result of the wavelength region of the light sequentially input from the wavelength region detection unit 110, the irradiation light amount of the light sequentially input from the irradiation light amount estimation unit 84, and the coefficient information 114. The determination of the coefficient, the multiplication of the coefficient by the irradiation light amount, and the output of the irradiation light amount after the multiplication are continuously executed.

The first notification control unit 86 of the fourth embodiment displays the latest irradiation light amount information 92 on the display unit 62A and outputs audio from the speaker 62B each time a new irradiation light amount after multiplication is input from the multiplication unit 112. Let me. Further, in the second notification control unit 88 of the fourth embodiment, each time a new irradiation light amount after multiplication is input from the multiplication unit 112, the irradiation light amount after the latest multiplication is larger than a predetermined upper limit value. If the amount of irradiation light becomes larger than the upper limit value, the warning information 94 is displayed on the display unit 62A and the speaker 62B outputs the sound.

As described above, in the fourth embodiment, since the irradiation light amount is estimated and the warning information 94 is notified in consideration of the wavelength range of the light emitted from the illumination system 18 to the eye E to be examined, the eye E to be examined is irradiated. The eye E to be inspected can be reliably protected from optical hazards regardless of the wavelength range of the light.

[Other]
FIG. 17 is an explanatory diagram for explaining an example of the display unit 62A. In each of the above embodiments, an external monitor such as a liquid crystal display has been described as an example of the display unit 62A for displaying the warning information 94, but the display unit 62A is, for example, a micro display (micro) provided in the lens barrel main body 24. A display projector) may also be used.

As shown in FIG. 17, the microdisplay type display unit 62A is the focal position (including the vicinity of the focal position) of the observation eye Eo for observing the anterior eye portion image 27 through the eyepiece 48, and the imaging position P. It is provided at a position adjacent to the anterior segment image 27 formed in (a position that does not interfere with the observation of the anterior segment image 27 by the observation eye Eo). Examples of such a display unit 62A include a reflective liquid crystal panel (Liquid crystal on silicon), a DMD (Digital Micro mirror Device), a MEMS (Micro Electro Mechanical Systems), an EL display (electroluminescence display), a transmissive liquid crystal display, and the like. A microscanner for image generation or the like is used.

The microdisplay type display unit 62A displays the above-mentioned irradiation light amount information 92 and warning information 94 under the control of the control unit 20 (first notification control unit 86 and second notification control unit 88). As a result, the examiner can confirm the irradiation light amount information 92 and the warning information 94 while observing the anterior eye portion image 27 without separating the observation eye Eo from the eyepiece portion 24a.

In each of the above embodiments, both the display unit 62A and the speaker 62B are used to notify the examiner of the irradiation light amount information 92 and the warning information 94, but only one of the display unit 62A and the speaker 62B is used to notify the examiner. You may.

In each of the above embodiments, an external monitor and a microdisplay have been described as an example of the display unit 62A, but for example, a meter panel and a lamp of a plurality of colors (the emission color changes as the amount of irradiation light increases, and a warning of optical hazards). In this case, various notification members (corresponding to the warning information notification unit and the irradiation light amount notification unit of the present invention) capable of transmitting the irradiation light amount information 92 and the warning information 94, such as red light emission), may be used.

FIG. 18 is a schematic view of the apparatus main body 200 of the ophthalmic apparatus of the present invention, which is different from the slit lamp microscope 10. In each of the above embodiments, the slit lamp microscope 10 has been described as an example of the ophthalmic apparatus of the present invention, but the present invention is not limited to the slit lamp microscope 10. For example, the present invention can be applied to various ophthalmic devices having a device body 200 as shown in FIG.

The apparatus main body 200 includes an irradiation system 202, a beam splitter 204, an optical element 206, and a photographing system 208 (light receiving system). The irradiation system 202 includes a light source 202a that emits various types of light. The beam splitter 204 is, for example, a half mirror, a dichroic mirror, or a polarizing beam splitter, and emits light incident from the irradiation system 202 toward the optical element 206, and emits light incident from the optical element 206 to the photographing system 208. Reflect toward. The optical element 206 includes, for example, an objective lens, and irradiates the eye E with the light incident from the beam splitter 204, and incidents the light reflected by the eye E on the beam splitter 204. The photographing system 208 includes an image pickup element 208a (light receiving element) that images (receives) the light from the eye E to be inspected reflected by the beam splitter 204.

By applying the present invention to various ophthalmic devices having such a device body 200, the eye E to be inspected can be protected from optical hazards as in each of the above embodiments. Examples of such an ophthalmic apparatus include an OCT apparatus that irradiates the eye E to be inspected with various types of light such as illumination light (observation light) or examination light, a fundus camera, and an SLO.

10 ... Narrow gap microscope 12 ... Jaw cradle 12a ... Jaw cradle 18 ... Lighting system 19 ... Observation system 20 ... Control unit 27 ... Anterior segment image 27D ... Captured image data 27R ... Region 29 ... Shooting system 31 ... Light source 53 ... Image pickup element 61 ... Storage unit 62A ... Display unit 62B ... Speaker 68 ... Operation unit 70 ... Detection unit 80 ... Drive condition acquisition unit 82 ... Irradiation time measurement unit 84 ... Irradiation light amount estimation unit 86 ... First notification control unit 88 ... Second Notification control unit 90 ... Corresponding information 92 ... Irradiation light amount information 94 ... Warning information 100 ... Light irradiation detection unit 102 ... Optical image 104 ... Irradiation position detection unit 106 ... Integrated map image 110 ... Wavelength range detection unit 112 ... Multiplying unit 114 ... Coefficient Information 200 ... Device body 202 ... Irradiation system 208 ... Imaging system

Claims (13)

An irradiation system that irradiates the eye to be inspected with the light emitted from the light source,
It is a drive condition acquisition unit that acquires the drive condition of the light source related to the intensity of light, and when the drive condition can be changed, the drive condition is acquired at least every time the drive condition is changed. Drive condition acquisition unit and
An irradiation time measuring unit that continuously measures the integrated irradiation time of the light to the eye to be inspected,
Based on the acquisition result of the drive condition acquisition unit and the measurement result of the irradiation time measurement unit, an irradiation light amount estimation unit that continuously estimates the irradiation light amount of the light to be irradiated to the eye to be inspected, and an irradiation light amount estimation unit.
An ophthalmic device equipped with. The ophthalmic apparatus according to claim 1, further comprising a warning information notification unit that notifies warning information when the irradiation light amount estimated by the irradiation light amount estimation unit becomes larger than a predetermined upper limit value. The ophthalmic apparatus according to claim 1 or 2, further comprising an irradiation light amount notification unit that notifies the irradiation light amount estimated by the irradiation light amount estimation unit. A storage unit that previously stores the correspondence between the driving conditions and the intensity of the light applied to the eye to be inspected is provided.
The irradiation light amount estimation unit determines the light intensity with reference to the correspondence relationship in the storage unit based on the acquisition result of the drive condition acquisition unit, and the measurement result of the light intensity and the irradiation time measurement unit. The ophthalmic apparatus according to any one of claims 1 to 3, wherein the irradiation light amount is estimated based on the above. A motion detection unit for detecting the on / off of the light source is provided.
The ophthalmologic apparatus according to any one of claims 1 to 4, wherein the irradiation time measuring unit measures the time when the light source is turned on as the integrated irradiation time based on the detection result of the motion detecting unit. A support mechanism that supports the irradiation system relative to the eye to be inspected and
A position detection unit that detects the position of the irradiation system and
With
Based on the detection result of the position detection unit, the time at which the irradiation time measuring unit is set within the irradiation position range of the light for the eye to be inspected in which the position of the irradiation system is predetermined is defined as the integrated irradiation time. The ophthalmic apparatus according to any one of claims 1 to 4. A chin rest that supports the subject's face,
A face detection unit that detects the presence or absence of support of the face by the chin rest, and
With
The method according to any one of claims 1 to 4, wherein the irradiation time measuring unit measures the time during which the chin rest supports the face as the integrated irradiation time based on the detection result of the face detecting unit. Ophthalmic device. An imaging system that continuously photographs the anterior segment of the eye to be inspected,
For each photographed image of the anterior segment photographed by the imaging system, a light irradiation detection unit that detects whether or not the light is irradiated to the anterior segment based on the captured image, and
With
The ophthalmic apparatus according to any one of claims 1 to 4, wherein the irradiation time measuring unit measures the integrated irradiation time based on the detection result of the light irradiation detecting unit for each captured image. Based on the detection result of the light irradiation detection unit, an irradiation position detection unit for detecting the irradiation position of the light in the photographed image is provided for each photographed image of the anterior eye portion irradiated with the light.
The irradiation time measuring unit continuously measures the integrated irradiation time for each of a plurality of regions in the captured image based on the detection result of the irradiation position detecting unit.
A claim that the irradiation light amount estimation unit continuously estimates the irradiation light amount for each of the plurality of regions based on the acquisition result of the driving condition acquisition unit and the measurement result of the irradiation time measurement unit for each of the plurality of regions. Item 8. The ophthalmic apparatus according to item 8. A wavelength range detection unit that detects the wavelength range of the light emitted to the eye to be inspected,
A multiplication unit that multiplies the irradiation light amount estimated by the irradiation light amount estimation unit based on the detection result of the wavelength range detection unit by a predetermined coefficient for each wavelength range.
The ophthalmic apparatus according to any one of claims 1 to 9. The ophthalmic apparatus according to any one of claims 1 to 10, wherein the drive condition acquisition unit acquires a drive voltage value or a drive current value of the light source as the drive condition. In the method of operating an ophthalmic apparatus including an irradiation system that irradiates an eye to be inspected with light emitted from a light source.
In the drive condition acquisition step of acquiring the drive condition of the light source related to the light intensity, and when the drive condition can be changed, the drive condition is acquired at least every time the drive condition is changed. Drive condition acquisition step and
An irradiation time measurement step for continuously measuring the integrated irradiation time of the light for the eye to be inspected,
Based on the acquisition result of the driving condition acquisition step and the measurement result of the irradiation time measurement step, the irradiation light amount estimation step for continuously estimating the irradiation light amount of the light to be irradiated to the eye to be inspected, and the irradiation light amount estimation step.
How to operate an ophthalmic device with. The method of operating an ophthalmic apparatus according to claim 12, further comprising a warning information notification step of notifying warning information when the irradiation light amount estimated in the irradiation light amount estimation step becomes larger than a predetermined upper limit value.

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