JP2020044281A - Ophthalmologic apparatus and operation method therefor - Google Patents

Abstract

To provide an ophthalmologic apparatus and an operation method therefor, capable of measuring an eye characteristic of a subject's eye even when the eye is a diseased one.SOLUTION: An ophthalmologic apparatus comprises; a target projection optical system in which a first luminous flux emission unit and one of first lenses are arranged so as to freely move back and forth along a first optical axis; a measurement pattern projection optical system in which a second luminous flux emission unit is arranged so as to freely move back and forth along a second optical axis; a light-receiving optical system including a second lens arranged so as to freely move back and forth along a third optical axis; an interlocked movement mechanism for moving the one, the second luminous flux emission unit, and the second lens in a parallel direction in parallel with the first optical axis in an interlocked manner; a movement control unit for executing movement processing of moving the one on the first optical axis; a stop operation reception unit for receiving a stop operation for stopping the movement processing; a stop control unit for stopping the movement processing; and a focusing position determination unit that on the basis of a stop position of the one stopped by the stop control unit, determines the one's focusing position for focusing a target luminous flux on the eyeground.SELECTED DRAWING: Figure 5

Description

  The present invention relates to an ophthalmologic apparatus that objectively measures (examines) eye characteristics of an eye to be inspected, and a method of operating the ophthalmologic apparatus.

  Ophthalmologic devices (such as refractometers and auto-refkeratometers) that objectively measure eye refractive power (such as spherical power, cylindrical power, and astigmatic axis angle) as eye characteristics of an eye to be examined are well known (Patent Documents) 1 to 3). In such an ophthalmologic apparatus, after performing automatic alignment for adjusting the focus of the optical system to the eye to be inspected, a ring-shaped measurement pattern is projected on the fundus of the eye to be inspected, and the measurement pattern reflected on the fundus is reflected. The fundus reflected light is imaged. Then, the ophthalmic apparatus analyzes the captured image of the fundus reflection light, detects a ring image corresponding to the measurement pattern from the captured image, obtains an approximate ellipse approximating the ring image, and calculates the shape of the approximate ellipse. The eye refractive power of the eye to be inspected is calculated based on (the major axis, the minor axis, and the axis angle).

JP 2017-63979 A JP 2018-38481 A JP-A-2006-159071

  FIG. 14 is an explanatory diagram showing an example of a captured image 23 obtained by capturing the fundus reflection light of the measurement pattern reflected on the fundus of the subject's eye. As shown in FIG. 14, in the ophthalmologic apparatus, the ring image 24 in the captured image 23 is used for calculating the eye refractive power in the ophthalmologic apparatus by adjusting the focus of the optical system to the fundus of the subject's eye (normal eye) by automatic alignment. The size becomes suitable, that is, the ring image 24 falls within the range of the scale 100 predetermined by the ophthalmologic apparatus. As a result, the eye refractive power of the eye to be inspected can be accurately obtained from the ring image 24. Therefore, in the ophthalmologic apparatus, it is desirable to adjust the focus of the optical system of the ophthalmic apparatus so that the ring image 24 falls within the range of the scale 100, and more preferably, within the scale 100a inside the scale 100. .

  However, when a disease such as refractive error (astigmatism) and cataract occurs in the subject's eye, the optical system does not focus on the fundus of the subject's eye even when automatic alignment is performed by the ophthalmic apparatus, and the subject is placed inside the scale 100. In some cases, the ring image 24 cannot be accommodated, or the ring image 24 cannot be detected from the captured image 23. In this case, the eye characteristics of the subject's eye may not be measured.

  The present invention has been made in view of such circumstances, and it is an object of the present invention to provide an ophthalmologic apparatus capable of measuring eye characteristics of an eye to be examined with a disease and an operation method thereof.

  An ophthalmologic apparatus for achieving the object of the present invention is a target projection optical system that has a first optical axis, projects a light flux of a target on the fundus of an eye to be examined, and emits a light flux of the target. An optotype having a first light beam emitting portion and a first lens through which the light beam of the optotype is transmitted, wherein one of the first light beam emitting portion and the first lens is arranged to be able to advance and retreat along the first optical axis. A measurement pattern projection optical system having a projection optical system, a second optical axis, and projecting a light beam of the measurement pattern onto the fundus; A measurement pattern projection optical system that is arranged to be able to advance and retreat along the optical axis; and a fundus reflection light of a light beam of the measurement pattern projected onto the fundus from the measurement pattern projection optical system having a third optical axis. A second lens, which is a light receiving optical system for receiving light and is arranged to be able to move forward and backward along a third optical axis. The movement of one of the light receiving optical systems having the first optical axis, the movement of the second light beam emitting unit along the second optical axis, and the movement of the second lens along the third optical axis are performed in conjunction with each other. An interlocking movement mechanism, an eye characteristic calculation unit that analyzes a ring image based on the fundus reflection light received by the light receiving optical system and calculates eye characteristics of the eye to be inspected, and controls the interlocking movement mechanism to control one of the first light A movement control unit that performs a movement process of moving along the axis, and a stop operation that receives a stop operation that stops the movement process at a position where the subject's eye subjectively recognizes the optotype during the execution of the movement process by the movement control unit. An operation receiving unit, a stop control unit that controls the interlocking movement mechanism to stop the moving process when the stop operation receiving unit receives the stop operation, and one of the stop units stopped on the first optical axis by the stop control unit. Based on the stop position, one of the A focus position determining unit that determines the focus position, a positioning control unit that controls the interlocking movement mechanism to position one of the focus positions determined by the focus position determiner, and one of the focus control units that has been moved to the focus position In this case, an objective expression including projection of a luminous flux of the measurement pattern onto the eye to be inspected by the measurement pattern projection optical system, reception of fundus reflected light by the light receiving optical system, and calculation of eye characteristics by the eye characteristics calculation unit. And an objective measurement control unit for performing the measurement.

  According to the present invention, since the second light beam emitting unit and the second lens can be positioned at the in-focus position with respect to the eye E estimated from the subjective test, the measurement projected onto the fundus from the measurement pattern projection optical system can be performed. The focus of the light beam of the pattern can be matched (substantially matched) with the fundus oculi Ef.

  In the ophthalmologic apparatus according to another aspect of the present invention, the first light beam emitting unit can selectively emit light beams of a plurality of types of optotypes having different visual acuity values, and controls the first light beam emitting unit to perform visual observation. An emission control unit that sequentially emits the light flux of the target for each type of optotype, and a movement control unit and a stop operation receiving unit each time the light flux of the optotype corresponding to the new visual acuity value is output from the first light output unit. And a repetition control unit that repeatedly operates the stop control unit. The focus position determination unit determines the focus position based on the stop position for each type of optotype. Accordingly, the in-focus position of the first lens can be determined even for the eye to be examined having a disease.

  In the ophthalmologic apparatus according to another aspect of the present invention, the focus position determination unit determines a stop position corresponding to a target having the highest visual acuity value among stop positions for each type of target as a focus position. . Accordingly, the in-focus position of the first lens can be determined even for the eye to be examined having a disease.

  In the ophthalmologic apparatus according to another aspect of the present invention, the focus position determination unit estimates a stop position corresponding to a target having a visual acuity value equal to or higher than a predetermined reference value based on the stop position for each type of target. The stop position is calculated, and the estimated stop position is determined as the focus position. Accordingly, the in-focus position of the first lens can be determined even for the eye to be examined having a disease.

  In the ophthalmologic apparatus according to another aspect of the present invention, the focus position determining unit generates correspondence information indicating a correspondence between the type of the optotype and the stop position, and calculates an estimated stop position based on the correspondence information. Accordingly, the in-focus position of the first lens can be determined even for the eye to be examined having a disease. Further, the correspondence information can be used for a subjective test using a separate device.

  In the ophthalmologic apparatus according to another aspect of the present invention, the emission control unit controls the first light flux emission unit to emit the light flux of the visual target in order from a visual target having a low visual acuity value. Thereby, the stop position of the first lens can be gradually brought closer to the eye to be examined.

  In the ophthalmologic apparatus according to another aspect of the present invention, the movement control unit controls the interlocking movement mechanism to move one of the movements in the traveling direction of the light flux of the target. Thus, the subject's eye can recognize the optotype during the movement processing of the first lens.

  In the ophthalmologic apparatus according to another aspect of the present invention, when the movement control unit controls the interlocking movement mechanism to execute the first movement processing, one of the movement control units moves along the traveling direction from the initial position at which the eye to be examined is fogged. When the second and subsequent movement processes are executed by controlling the interlocking movement mechanism, one of them is moved along the traveling direction from the previous stop position.

  In the ophthalmologic apparatus according to another aspect of the present invention, the second light beam emitting unit emits a light beam having a ring-shaped measurement pattern.

  An ophthalmologic apparatus according to another aspect of the invention includes a pair of optotype projection optical systems corresponding to both eyes, a pair of measurement pattern projection optical systems, and a pair of light receiving optical systems.

  In the ophthalmologic apparatus according to another aspect of the present invention, the first optical axis, the second optical axis, and the third optical axis are parallel to each other.

  An operation method of an ophthalmologic apparatus for achieving the object of the present invention is an optotype projection optical system that has a first optical axis, projects an optotype light beam onto the fundus of an eye to be inspected, and includes an optotype light beam. And a first lens through which the light beam of the target passes. One of the first light beam emitting portion and the first lens is arranged to be able to advance and retreat along the first optical axis. A measurement target projection optical system that has a second optical axis and projects a light flux of the measurement pattern onto the fundus, and emits a light flux of the measurement pattern. A measurement pattern projection optical system which is arranged to be able to advance and retreat along the second optical axis, and a fundus of a light beam of the measurement pattern projected onto the fundus from the measurement pattern projection optical system, having the third optical axis. A light receiving optical system for receiving reflected light, and is disposed to be able to move forward and backward along the third optical axis. A light receiving optical system having two lenses, one movement along the first optical axis, the movement of the second light beam emitting unit along the second optical axis, and the movement of the second lens along the third optical axis The method of operating an ophthalmologic apparatus, comprising: an interlocking movement mechanism that performs the operation and an eye characteristic calculation unit that analyzes a ring image based on fundus reflection light received by the light receiving optical system and calculates eye characteristics of the eye to be examined. The control unit controls the interlocking movement mechanism to perform a movement process of moving one along the first optical axis, and the stop operation receiving unit performs the movement process by the movement control unit. A stop operation receiving step of receiving a stop operation for stopping the movement process at a position where the subject's eye has perceived the target visually, and a stop control unit that operates when the stop operation is received by the stop operation receiving unit. System that stops movement processing by controlling A focusing step for determining one focus position for focusing the light beam of the target on the fundus based on the one stop position stopped on the first optical axis by the stop control unit. One of the position determination step, the positioning control step of controlling the interlocking movement mechanism to position one of the two at the focus position determined by the focus position determination section, and the objective measurement control step When moved to the in-focus position, the measurement pattern projection optical system projects the luminous flux of the measurement pattern onto the eye to be inspected, the light receiving optical system receives the fundus reflected light, and the eye characteristic calculation unit calculates the eye characteristics. And an objective measurement control step of causing the objective measurement to be performed.

  INDUSTRIAL APPLICABILITY The present invention can measure eye characteristics of a subject's eye with a disease.

It is a schematic diagram of the ophthalmologic apparatus of the present invention. FIG. 3 is a block diagram illustrating a configuration of an optical system of the ophthalmologic apparatus. It is an explanatory view for explaining an example of a plurality of kinds of optotype charts formed on a chart plate. It is a functional block diagram of a control device. It is explanatory drawing for demonstrating the 1st movement process by each part of the subjective test | inspection control part corresponding to the optotype chart of visual acuity value "0.1", stop operation acceptance, and stop control. It is explanatory drawing for demonstrating the 2nd movement process by each part of the subjective test | inspection control part corresponding to the optotype chart of the visual acuity value "0.2", stop operation reception, and stop control. To explain the lens position of the focusing lens after completion of the fifth movement process, stop operation acceptance, and stop control by each unit of the subjective test control unit corresponding to the optotype chart of the visual acuity value of “0.8” FIG. FIG. 4 is an explanatory diagram for describing a method of determining a focus position of a focusing lens by a focus position determination unit. FIG. 4 is an explanatory diagram showing an example of an operation screen displayed on a monitor in a re-measurement mode. 9 is a flowchart illustrating a flow of an objective measurement process of the eye refractive power of the eye to be inspected by the ophthalmologic apparatus, particularly a flow of a measurement process of the eye refractive power in the re-measurement mode. FIG. 4 is an explanatory diagram for describing a captured image (ring image) acquired in a re-measurement mode. It is the schematic of the ophthalmologic apparatus of another Embodiment 1. It is the schematic of the optotype projection optical system, the measurement pattern projection optical system, and the light-receiving optical system of the ophthalmologic apparatus of another Embodiment 2. FIG. 5 is an explanatory diagram showing an example of a captured image obtained by capturing the fundus reflection light of the measurement pattern reflected by the fundus of the subject's eye.

[Configuration of Ophthalmic Device]
FIG. 1 is a schematic diagram of an ophthalmologic apparatus 1 of the present invention. As shown in FIG. 1, the ophthalmologic apparatus 1 is an auto-refkeratometer or the like capable of measuring an eye refractive power or the like as eye characteristics of the eye E to be examined, and includes a base 2, a face receiving section 3, a gantry 4, and a measuring head. 5 is provided.

  It should be noted that the X-axis direction in the figure is the left-right direction (the interpupillary direction of the eye E) with respect to the subject, the Y-axis direction is the up-down direction, and the Z-axis direction is the subject (the eye E). ) And a back and forth direction (also referred to as a working distance direction) parallel to a front direction approaching the subject and a rear direction moving away from the subject.

  The face receiving portion 3 is provided integrally with the base 2 at a position on the front side in the Z-axis direction of the measuring head 5. The face receiving portion 3 has a chin rest 3a and a forehead rest 3b whose position can be adjusted in the Y-axis direction, and supports the face of the subject.

  The gantry 4 is provided on the base 2 and is movable with respect to the base 2 in each of XZ-axis directions (front-back, left-right directions). A measuring head 5 and an operation lever 6 are provided on the gantry 4.

  The operation lever 6 is provided on the gantry 4 and at a position on the rear side (examiner side) of the measurement head 5 in the Z-axis direction, and is operated when the measurement head 5 is moved in each direction of the XYZ axes. Operating member. For example, when the operation lever 6 is tilted in the Z-axis direction (front-back direction) or the X-axis direction (left-right direction), the measuring head 5 is moved in the Z-axis direction or the X-axis direction by an electric drive mechanism (not shown). . When the operation lever 6 is rotated around its longitudinal axis, the measuring head 5 is moved in the Y-axis direction (up-down direction) by the above-described electric drive mechanism according to the rotation operation direction. Note that a measurement button for starting the measurement of the eye refractive power and the like of the eye E by the ophthalmologic apparatus 1 is provided at the top of the operation lever 6.

  The measurement head 5 has a function of measuring eye characteristics (eye refractive power and corneal shape) of the eye E to be examined. A monitor 7 is provided on the rear surface of the measuring head 5 in the Z-axis direction. In the measuring head 5, an optical system 8 (including an image sensor, various light sources, and various driving units) corresponding to the measurement of eye refractive power and the like, and a control device 9 are provided.

  The monitor 7 is, for example, a touch panel type liquid crystal display device. The monitor 7 displays an observation image 22 (see FIG. 9) of the anterior segment of the eye E to be used for alignment of the measurement head 5 and the like, and a measurement result of the eye refractive power of the eye E obtained by the measurement head 5. , And an input screen for performing an operation (setting) related to the measurement. In addition, the monitor 7 displays an observation image 22 of the anterior segment, a captured image 23 (ring image 24), and an operation screen 25 showing a measurement state and the like in the re-measurement mode, as shown in FIG.

  As the control device 9, various types of arithmetic processing devices are used. The control device 9 performs overall control of the operation of each unit of the ophthalmologic apparatus 1 and calculates the eye refractive power and the like of the eye E to be examined. Note that a spectacle lens measuring device (not shown) can be connected to the control device 9, and measurement data (such as a lens power) of the spectacle lens worn by the subject is input from the spectacle lens measuring device.

[Optical system of ophthalmic device]
FIG. 2 is a block diagram illustrating a configuration of the optical system 8 of the ophthalmologic apparatus 1. As shown in FIG. 2, the optical system 8 includes an observation optical system 12, a Z alignment optical system 13, an XY alignment optical system 14, an optotype projection optical system 15, a measurement pattern projection optical system 16, An optical system 17.

(Configuration of observation optical system)
The observation optical system 12 is an optical system used for observing the anterior segment of the eye E to be examined, and photographs the anterior segment. The observation optical system 12 has a main optical axis O1 parallel to the Z-axis direction. In the observation optical system 12, the objective lens 12a, the dichroic filter 12b, the half mirror 12c, the relay lens 12d, the dichroic filter 12e, and the A lens 12f and an image sensor 12g of a complementary metal oxide semiconductor (CMOS) type or a charge coupled device (CCD) type are arranged. The observation optical system 12 has an illumination light source (not shown). In addition, since each part which comprises the observation optical system 12 is a well-known technique, the detailed description is omitted.

  The illumination light emitted from the illumination light source of the observation optical system 12 illuminates the anterior segment of the eye E and is reflected by the anterior segment. The reflected light is incident on the observation optical system 12, and is incident on the imaging surface of the imaging element 12g via each part of the observation optical system 12. As a result, the reflected light is imaged by the imaging element 12g, and captured image data of the observation image 22 of the anterior segment of the eye E is acquired by the imaging element 12g. The imaging element 12g outputs the captured image data of the observation image 22 to the control device 9.

  A kerat plate 12h and a kerat ring light source 12i used for measuring the corneal shape of the cornea Ec of the eye E are provided around the objective lens 12a. The kerato plate 12h and the kerat ring light source 12i project a single or multiple ring-shaped light beams onto the cornea Ec of the anterior segment. The ring-shaped light beam reflected by the cornea Ec is incident on the imaging surface of the imaging element 12g via the objective lens 12a, the dichroic filter 12b, and the like. Thereby, a kerattling image is captured by the image sensor 12g. The imaging element 12g outputs the captured image data of the kerattling image to the control device 9.

(Z alignment optical system)
The Z alignment optical system 13 is used for detecting an alignment state of the measuring head 5 with respect to the eye E in the Z axis direction. The Z alignment optical system 13 is provided at two locations behind the kerato plate 12h (on the side of the image sensor 12g). Each Z alignment optical system 13 has an alignment light source 13a and a projection lens 13b. Each alignment light source 13a emits a light beam toward the projection lens 13b. A pair of light beams emitted from each alignment light source 13a is converted into a parallel light beam by each projection lens 13b, and then transmitted through a pair of transmission holes (not shown) of the kerato plate 12h and projected onto the cornea Ec. .

  The pair of light beams reflected by the cornea Ec enter the imaging surface of the imaging element 12g via the objective lens 12a, the dichroic filter 12b, and the like. As a result, a pair of bright spot images are captured by the imaging element 12g, and the imaging element 12g outputs captured image data of the pair of bright spot images to the control device 9. Thus, a pair of bright spot images can be displayed on the monitor 7 together with the above-described observation image 22 and kerattling image. Then, the control device 9 drives the electric drive mechanism (not shown) automatically or manually by the examiner, for example, so that the kerattling image and the pair of bright spot images have a predetermined positional relationship. By moving 5 in the Z-axis direction, alignment in the Z-axis direction (Z alignment) is performed. The Z alignment may use another known method.

(XY alignment optical system)
The XY alignment optical system 14 is used for detecting an alignment state of the measurement head 5 with respect to the eye E in the X-axis direction and the Y-axis direction. The XY alignment optical system 14 forms an optical path branched from the observation optical system 12 via the half mirror 12c. The XY alignment optical system 14 has an alignment light source 14a and a projection lens 14b. The alignment light source 14a emits a light beam toward the projection lens 14b. The light beam emitted from the alignment light source 14a is converted into a parallel light beam by the projection lens 14b, reflected by the half mirror 12c, and projected on the cornea Ec via the dichroic filter 12b and the objective lens 12a.

  The light beam reflected by the cornea Ec enters the imaging surface of the imaging device 12g via the objective lens 12a, the dichroic filter 12b, and the like. Thereby, the bright spot image is captured by the image sensor 12g, and the image sensor 12g outputs the captured image data of the bright spot image to the control device 9. This allows the monitor 7 to display a bright spot image for XY alignment together with the observation image 22, the kerattling image, and the pair of bright spot images. Then, the control device 9 automatically or the examiner manually drives an electric driving mechanism (not shown) to adjust the positions of the bright spot images in the X-axis direction and the Y-axis direction, so that the X-axis direction and the Y-axis Directional alignment (XY alignment) is performed. The XY alignment may use another known method.

(Configuration of optotype projection optical system)
The target projecting optical system 15 projects the light flux of the fixation target onto the fundus oculi Ef of the eye E to fixate or fog the eye E at the time of objective measurement of the eye refractive power of the eye E, and will be described later. During the subjective test in the re-measurement mode, the luminous flux of the optotype chart 26 (see FIG. 3) is projected on the fundus oculi Ef.

  The target projection optical system 15 includes an LED light source 15a using an LED (light emitting diode) that generates white light, a color correction filter 15b, a collimator lens 15c, a chart plate 15d, a half mirror 15e, and a relay lens 15f. , A reflection mirror 15g, a focusing lens 15h (also referred to as a moving lens), a relay lens 15i, a field lens 15j, a VCC lens 15k which is a variable cross cylinder lens, and a reflection mirror 15m. , Dichroic filters 15n and 12b and an objective lens 12a. In addition, since each part which comprises the optotype projection optical system 15 is a well-known technique, the detailed description is abbreviate | omitted.

  The target projection optical system 15 has a glare light source 15p used for a glare test of the eye E. The glare light source 15p emits glare light to the half mirror 15e during a glare test. As a result, glare light is applied to the eye E through each part from the half mirror 15e to the objective lens 12a.

  The chart plate 15d is a disc on which a plurality of targets are formed. The chart plate 15d has a rotation axis parallel to the optical path 15q of the white light emitted from the LED light source 15a. The chart plate 15d is rotationally driven by a chart plate driving mechanism 20 (constituted by a motor or the like) connected to the rotation axis, thereby selectively inserting any one of the plurality of targets into the optical path 15q. I do. Thus, the target inserted into the optical path 15q is illuminated by the white light that is incident from the LED light source 15a via the color correction filter 15b and the collimator lens 15c. As a result, the luminous flux of the target is emitted from the chart plate 15d toward the half mirror 15e, and further, the luminous flux of the target is projected onto the fundus oculi Ef via each part from the half mirror 15e to the objective lens 12a.

  Note that the chart plate 15d, together with the LED light source 15a, the color correction filter 15b, and the collimator lens 15c, constitutes a first light beam emitting unit of the present invention. In addition, instead of the chart plate 15d and the like, a liquid crystal display (liquid crystal display: LCD), a micro display (also referred to as a micro display projector), which can emit a light beam of an arbitrary target, as a first light beam emitting unit of the present invention, A transmissive LCD, a micro scanner for generating an image, or the like may be used. Further, these LCDs and the like may be arranged on the optical axis O2.

  A fixation target and a target chart 26 (see FIG. 3) are formed on the chart plate 15d as a plurality of types of targets. The fixation target is a fixation target for fixing or clouding the eye E to be inspected, and for example, a landscape chart or the like is used.

  FIG. 3 is an explanatory diagram illustrating an example of a plurality of types of optotype charts 26 formed on the chart plate 15d. As shown in FIG. 3, each optotype chart 26 is an optotype (Randle ring) used for a subjective test of the visual acuity value of the eye E, and is formed on the chart board 15 d for each visual acuity value. Each of the optotype charts 26 is selectively inserted into the optical path 15q by the chart plate drive mechanism 20 rotatingly driving the chart plate 15d. As a result, the luminous fluxes of the plurality of optotype charts 26 having different visual acuity values are selectively emitted from the chart plate 15d toward the half mirror 15e, and the luminous fluxes pass through the respective portions from the half mirror 15e to the objective lens 12a to form the fundus. Projected to Ef. These optotype charts 26 are used in a subjective test in a re-measurement mode described later.

  The type of the optotype chart 26 used in the re-measurement mode described below is not limited to the Landolt ring shown in FIG. Any target such as the target chart 26 (E character target) or a landscape chart can be used.

  Returning to FIG. 2, the optotype projection optical system 15 has an optical axis O2 (corresponding to the first optical axis of the present invention) parallel to the above-described main optical axis O1. On this optical axis O2, a focusing lens 15h, a relay lens 15i, a field lens 15j, a VCC lens 15k, and the like are arranged.

  The focusing lens 15h corresponds to the first lens and “one” of the present invention, and is disposed to be able to advance and retreat along the optical axis O2 of the target projection optical system 15. The focusing lens 15h is moved forward and backward on the optical axis O2 by an interlocking movement mechanism 27 described later. In the present embodiment, the lens position of the focusing lens 15h is represented by a diopter (D) conversion value.

  As shown by the arrow "minus [D]" in the figure, the lens position on the optical axis O2 of the focusing lens 15h is determined by the direction of the luminous flux of the optotype (fixation target, optotype chart 26), that is, the eye to be inspected. By moving to the E side, the refractive power of the luminous flux of the optotype can be displaced to the minus side. Conversely, as shown by the arrow “plus [D]” in the figure, the lens position of the focusing lens 15 h is moved away from the eye E, so that the refractive power of the luminous flux of the target becomes positive. Can be displaced. Therefore, the presenting distance of the optotype chart 26 to the eye E can be changed by moving the focusing lens 15h forward and backward. Further, the eye E can be fixed or clouded by the fixation target.

  The VCC lens 15k has a pair of positive and negative cylinder lenses. The pair of cylinder lenses are independently rotatable about the optical axis O2. The VCC lens 15k has a function of correcting (correcting) a cylindrical power (astigmatic power) and an axial angle (astigmatic axis angle) among aberrations caused by the refraction characteristics of the eye E to be inspected.

  The VCC lens 15k is driven by a VCC lens driving mechanism 19 (see FIG. 4) including a motor and the like under the control of the control device 9. The astigmatic power can be adjusted by rotating the pair of cylinder lenses in opposite directions by the VCC lens drive mechanism 19, and the astigmatic axis angle can be adjusted by integrally rotating the cylinder lenses in the same direction.

(Configuration of measurement pattern projection optical system)
The measurement pattern projection optical system 16 projects a light beam of a ring-shaped measurement pattern (hereinafter, simply referred to as a measurement pattern) used for measuring the objective eye refractive power of the eye E to be examined on the fundus oculi Ef. The measurement pattern projection optical system 16 includes a reflex measurement unit 16a, a relay lens 16b, a pupil ring 16c, a field lens 16d, a perforated prism 16e, a rotary prism 16f, a dichroic filter 15n, and a dichroic filter 12b. , An objective lens 12a. In addition, since each part which comprises the pattern projection optical system 16 for a measurement is a well-known technique, the description about the detail is abbreviate | omitted.

  The measurement pattern projection optical system 16 has an optical axis O3 (corresponding to the second optical axis of the present invention) parallel to the above-described main optical axis O1 and optical axis O2. On this optical axis O2, a reflex measurement unit 16a, a relay lens 16b, a pupil ring 16c, a field lens 16d, and a perforated prism 16e are arranged.

  The reflex measurement unit 16a corresponds to the second light beam emitting unit of the present invention, and includes an LED light source 16h, a collimator lens 16i, a conical prism 16j, and a measurement pattern forming plate 16k. Note that the LED light source 16h and the pupil ring 16c are arranged at optically conjugate positions. The forming plate 16k and the fundus oculi Ef are arranged at optically conjugate positions.

  The reflex measurement unit 16a is arranged to be able to advance and retreat along the optical axis O3 of the measurement pattern projection optical system 16. The reflex measurement unit 16a is moved forward and backward on the optical axis O3 by an interlocking movement mechanism 27 described later.

  The light beam emitted from the LED light source 16h is converted into parallel light by the collimator lens 16i, and then is converted into a light beam of a measurement pattern via the conical prism 16j and the forming plate 16k. Thereby, the light flux of the measurement pattern is emitted toward the relay lens 16b. This light flux passes through a relay lens 16b, a pupil ring 16c, a field lens 16d, a reflection surface of a perforated prism 16e, a rotary prism 16f, a dichroic filter 15n, a dichroic filter 15n, a dichroic filter 12b, and a fundus Ef through an objective lens 12a. Projected. The luminous flux of the measurement pattern is projected onto the fundus oculi Ef in a state where its shape is distorted by the eye refractive power of the eye E.

(Configuration of light receiving optical system)
The light receiving optical system 17 receives (detects) the fundus reflection light of the luminous flux of the measurement pattern projected on the fundus oculi Ef by the measurement pattern projection optical system 16. The light receiving optical system 17 includes an objective lens 12a, dichroic filters 12b and 15n, a rotary prism 16f, a perforated prism 16e, a field lens 17a, a reflection mirror 17b, a relay lens 17c, and a focusing lens 17d (moving Lens), a reflection mirror 17e, a dichroic filter 12e, an imaging lens 12f, and an image sensor 12g. Since the components constituting the light receiving optical system 17 are known technologies, detailed description thereof will be omitted.

  The light receiving optical system 17 has the above-described main optical axis O1, optical axis O2, and optical axis O4 parallel to the optical axis O3 (corresponding to the third optical axis of the present invention). A reflection mirror 17b, a relay lens 17c, a focusing lens 17d, and a reflection mirror 17e are arranged on the optical axis O4.

  The focusing lens 17d corresponds to the second lens of the present invention, and is disposed so as to be able to advance and retreat along the optical axis O4 of the light receiving optical system 17. The focusing lens 17d is moved forward and backward on the optical axis O4 by an interlocking movement mechanism 27 described later.

  The fundus reflection light of the luminous flux of the measurement pattern reflected by the fundus Ef includes the objective lens 12a, the dichroic filters 12b and 15n, the rotary prism 16f, the hole of the perforated prism 16e, the field lens 17a, the reflection mirror 17b, and the relay lens. The light enters the light receiving surface of the image sensor 12g via the focusing lens 17c, the focusing lens 17d (also referred to as a moving lens), the reflection mirror 17e, the dichroic filter 12e, and the imaging lens 12f. The imaging element 12g captures the fundus reflection light and outputs captured image data of the captured image 23 of the fundus reflection light to the control device 9.

  Although not shown, the interlocking movement mechanism 27 includes a holding member that integrally holds (connects) the focusing lens 15h, the reflex measurement unit 16a, and the focusing lens 17d, and a main optical axis O1 (each light beam). A slide mechanism for holding the slide member slidably in a direction parallel to the axes O2 to O4) (Z axis direction) and a drive mechanism such as a motor for moving the holding member forward and backward in the Z axis direction are provided. Accordingly, the focusing lens 15h, the reflex measurement unit 16a, and the focusing lens 17d are moved along the Z-axis direction (integrally) by the interlocking movement mechanism 27. Here, the movement in conjunction (cooperative movement) refers to a direction in which the focusing lens 15h, the reflex measurement unit 16a, and the focusing lens 17d move toward or away from the eye E on each of the optical axes O2 to O4. Is moved by the same amount of movement.

[Configuration of control device]
FIG. 4 is a functional block diagram of the control device 9. As shown in FIG. 4, the control device 9 includes an arithmetic circuit including various processors and memories. Various processors include a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), and a programmable logic device [for example, SPLD (Simple Programmable Logic Devices), CPLD (Complex Programmable Logic Device), And FPGA (Field Programmable Gate Arrays)]. The various functions of the control device 9 may be realized by one processor, or may be realized by a plurality of same or different processors.

  The control device 9 executes a control program read out from a storage unit (not shown) based on an input operation of the examiner on the operation lever 6 and the touch panel type monitor 7, thereby integrally controlling the operation of each unit of the ophthalmologic apparatus 1. Control. The control device 9 includes, in addition to the operation lever 6 and the monitor 7, the image pickup device 12g of the optical system 8 described above, the kerattling light source 12i, the alignment light sources 13a and 14a, the LED light source 15a, the glare light source 15p, and the LED light source 16h. , A VCC lens drive mechanism 19, a chart plate drive mechanism 20, an interlocking movement mechanism 27, and the like. The control device 9 is connected to an operation switch 29 that is operated by the subject in a re-measurement mode described later.

  The control device 9 functions as an operation control unit 30, an alignment control unit 32, a measurement control unit 34, and an eye characteristic calculation unit 36 by executing the above-described control program. Hereinafter, what is described as the “unit” in the present embodiment may be “the circuit”, “the device”, or “the device”. That is, what is described as the “unit” may be configured by any of firmware, software, hardware, or a combination thereof.

  The operation control unit 30 includes a light source control unit 40, a drive control unit 42, an imaging control unit 44, a display control unit 46, a chart plate drive control unit 48, and a VCC lens drive control unit 50.

  The light source control unit 40 controls each light source (kerattling light source 12i, alignment light sources 13a and 14a, LED light source 15a, glare light source 15p, and LED light source connected to the control device 9 under the control of the measurement control unit 34 described later). 16h).

  The drive control unit 42 drives an electric drive mechanism (not shown) in accordance with an operation (tilt operation and rotation operation) on the operation lever 6 to move the measuring head 5 in each of the XYZ axes. Further, the drive control unit 42 drives the interlocking movement mechanism 27 under the control of the measurement control unit 34 to be described later to interlock (integrally) the focusing lens 15h, the reflex measurement unit 16a, and the focusing lens 17d. ) Move along the Z-axis direction.

  The imaging control unit 44 drives the imaging element 12g under the control of the measurement control unit 34, which will be described later, and performs the above-described observation image 22, a pair of bright spot images for Z alignment, a bright spot image for XY alignment, And the imaging of each of the captured image data of the captured image 23 is executed.

  The display control unit 46 controls image display on the monitor 7. The display control unit 46 causes the monitor 7 to display an observation image 22, a captured image 23 (ring image 24), and an operation screen 25 (see FIG. 9) showing a measurement state and the like in a re-measurement mode described later.

  The chart plate drive control unit 48 drives the chart plate drive mechanism 20 to rotate the chart plate 15d under the control of the measurement control unit 34, which will be described later, so that a plurality of optotypes formed on the chart plate 15d ( The fixation target and the target chart 26) are selectively inserted into the optical path 15q. Thereby, the luminous flux of the optotype can be projected from the optotype projection optical system 15 to the fundus oculi Ef for each type of optotype.

  When the measurement result of the astigmatic state (degree of astigmatism and astigmatic axis) of the eye E obtained by known objective measurement or the like is input to the touch panel type monitor 7, the VCC lens drive control unit 50 performs this measurement. Based on the result, the VCC lens driving mechanism 19 is driven to rotate the pair of cylinder lenses, thereby correcting the astigmatic state of the eye E to be inspected.

  The alignment control unit 32 controls each unit of the operation control unit 30 before starting the objective measurement of the eye characteristics of the eye E to perform alignment (automatic alignment or manual alignment) of the measurement head 5 with respect to the eye E. Execute. Note that this alignment is performed in a state where the fixation target (scenery chart) is fixed on the eye E to be inspected. However, a specific method is a known technique, and a description thereof will be omitted.

  The measurement control unit 34 controls each unit of the operation control unit 30 to perform an objective measurement and a subjective test of the eye characteristics (eye refractive power in this case) of the eye E to be inspected. Note that the measurement of the corneal shape is basically the same as the conventional method, and a specific description thereof will be omitted. Hereinafter, the eye characteristics of the eye to be examined E indicate characteristics (eye refractive power in the present embodiment) obtained by analyzing the ring image 24.

  The measurement control unit 34 has an objective measurement mode, a subjective examination mode, and a re-measurement mode as measurement modes for measuring the eye characteristics of the eye E to be inspected. These measurement mode switching operations are executed in response to a mode switching operation input to the touch panel type monitor 7.

  When the objective measurement mode is selected, the measurement control unit 34 controls each unit of the operation control unit 30 to execute the objective measurement of the eye refractive power of the eye E to be inspected. In this case, after the above-described alignment is performed, the measurement control unit 34 drives the interlocking movement mechanism 27 via the drive control unit 42 to move the focusing lens 15h by + 1.5D, and the eye to be examined Let E be a cloud fogging state. Next, the measurement control unit 34 controls the light source control unit 40 to turn on the LED light source 16h, and causes the measurement pattern projection optical system 16 to project the luminous flux of the measurement pattern onto the fundus oculi Ef. Then, the measurement control unit 34 controls the imaging control unit 44 to cause the imaging device 12g to perform imaging of the fundus reflection light of the measurement pattern reflected by the fundus oculi Ef. 36, the output of the captured image data of the captured image 23 is executed.

  When the subjective test mode is selected, the measurement control unit 34 controls each unit of the operation control unit 30 to perform a subjective test (a distance test, a near test, a contrast test, and a glare test) of the eye characteristics of the eye E to be examined. Etc.). In this case, the measurement control unit 34 controls the light source control unit 40 to turn on the LED light source 15a, and also drives the chart plate drive mechanism 20 to perform a visual inspection target (the target chart 26 or the like) of the chart plate 15d. ) Is inserted into the optical path 15q. As a result, the luminous flux of the optotype for the subjective examination is projected from the optotype projection optical system 15 onto the fundus oculi Ef, and the subject responds to the optotype for the subjective examination. When performing the glare inspection, the measurement control unit 34 controls the light source control unit 40 to turn on the glare light source 15p.

  When the re-measurement mode is selected, the measurement control unit 34 controls each unit of the operation control unit 30 to execute the re-measurement of the objective measurement of the eye refractive power of the eye E to be examined. This re-measurement mode is executed when the objective measurement of the eye refractive power of the eye E cannot be performed in the objective measurement mode described above. The case where the objective measurement is not possible means that the focus of the luminous flux of the measurement pattern emitted from the measurement pattern projection optical system 16 deviates from the fundus Ef even after the alignment is completed due to a disease or the like of the eye E. Or the ring image 24 cannot be detected from the captured image 23. When the re-measurement mode is selected, the measurement control unit 34 executes the objective examination of the eye E in combination with the objective examination of the eye E, which will be described later in detail.

  The eye characteristic calculation unit 36 analyzes the captured image data of the captured image 23 input from the image sensor 12g, detects the ring image 24 from the captured image 23, and analyzes the shape of the ring image 24 (such as ellipse approximation). Is performed, and the eye refractive power of the eye E is calculated based on the shape analysis result of the ring image 24. Since a specific calculation method of the eye refractive power is a known technique, a specific description is omitted here.

(Remeasurement mode)
Next, the re-measurement mode will be described. When the measurement control unit 34 is switched to the re-measurement mode, the measurement control unit 34 first performs a subjective test of the eye E to be inspected, and the eye E to be inspected for each of the plurality of types of optotype charts 26 having different visual acuity values. Of the focusing lens 15h (stop position to be described later) that can be recognized. Next, based on the lens position (stop position) of the focusing lens 15h for each of the optotype charts 26, the measurement control unit 34 determines the in-focus position of the in-focus lens 15h that focuses the light flux of the optotype chart 26 on the fundus oculi Ef. (Estimated value). Then, after positioning the focusing lens 15h at the in-focus position, the measurement control unit 34 again performs the objective measurement of the eye characteristics of the eye E to be inspected.

  In the re-measurement mode, the measurement control unit 34 functions as a subjective inspection control unit 52, a focus position determination unit 54, a positioning control unit 56, and an objective measurement control unit 58.

  When the measurement control unit 34 is switched to the re-measurement mode, the subjective test control unit 52 performs the subjective test of the subject's eye E for determining the focus position described above. In this subjective examination, presentation of the optotype chart 26 to the eye E to be inspected, a movement process of moving the focusing lens 15h along the optical axis O2, and a process of moving the focusing lens 15h subjectively to the eye E And the stop control of the movement process are repeatedly executed for each of the plurality of optotype charts 26 having different visual acuity values. Therefore, the subjective inspection control unit 52 functions as an emission control unit 52a, a movement control unit 52b, a stop operation reception unit 52c, a stop control unit 52d, and a repetition control unit 52e.

  When the measurement control unit 34 is switched to the re-measurement mode, the emission control unit 52a controls the light source control unit 40 to turn on the LED light source 15a, and controls the chart plate driving mechanism 20 via the chart plate drive control unit 48. By driving, the optotype chart 26 having the lowest visual acuity value in the chart plate 15d is inserted into the optical path 15q. Thereby, the light flux of the optotype chart 26 having the visual acuity value “0.1” is projected on the fundus oculi Ef.

  In addition, the emission control unit 52a drives the chart board driving mechanism 20 via the chart board drive control unit 48 in response to the input of the optotype switching operation to the monitor 7, and the second visual acuity in the chart board 15d. The optotype chart 26 having a low value is inserted into the optical path 15q. Thereby, the light flux of the optotype chart 26 having the visual acuity value “0.2” is projected on the fundus oculi Ef.

  Hereinafter, the emission control unit 52a drives the chart board driving mechanism 20 via the chart board drive control unit 48 every time the optotype switching operation is input to the monitor 7, and thereby the remaining optotype chart 26 Are inserted into the optical path 15q in order from the one with the lowest visual acuity value. As a result, the luminous flux of the optotype chart 26 is projected from the optotype projection optical system 15 to the fundus oculi Ef in order from the one with the lowest visual acuity value. In the subjective test according to the present embodiment, a total of 6 visual acuity values of “0.1”, “0.2”, “0.3”, “0.5”, “0.8”, and “1.0” were obtained. Although the type of the target chart 26 is used, the type of the target chart 26 may be appropriately increased or decreased.

  When the optotype chart 26 having the visual acuity value “0.1” is presented to the eye E to be examined, the movement control unit 52b drives the interlocking movement mechanism 27 via the drive control unit 42 to move the focusing lens 15h. The eye E is moved to an initial position which is a lens position for fogging the eye E (for example, + 1.5D when the eye E is myopic, see FIG. 5 described later). Next, the movement control unit 52b drives the interlocking movement mechanism 27 via the drive control unit 42 to move the focusing lens 15h from the initial position in the minus [D] direction along the optical axis O2 for the first time. Perform processing. Thereby, the subject's eye E can recognize the optotype chart 26. In this case, the lower the visual acuity value of the eye E, the larger the moving amount of the focusing lens 15h.

  Then, the movement control unit 52b continues the first movement processing of the focusing lens 15h until it is stopped by the stop control unit 52d described later. In conjunction with the movement of the focusing lens 15h, the reflex measuring unit 16a and the focusing lens 17d are also moved integrally in the minus [D] direction by the interlocking movement mechanism 27.

  Further, the movement control unit 52b drives the interlocking movement mechanism 27 via the drive control unit 42 every time a repetition control command is input from the repetition control unit 52e described below in response to the optotype switching operation described above. Then, the second and subsequent movement processes for moving the focusing lens 15h in the minus [D] direction along the optical axis O2 from the previous stop position are executed. Note that the movement control unit 52b continues the second and subsequent movement processing until it is stopped by the stop control unit 52d described later.

  The stop operation receiving unit 52c receives a stop operation of the movement process input to the monitor 7 or the operation switch 29 of the touch panel type while the movement control unit 52b is performing the movement process of the focusing lens 15h. This stop operation is an operation for stopping the movement processing at the position where the eye E has subjectively recognized the optotype chart 26. For example, when the subject recognizes the optotype chart 26 during the moving process of the focusing lens 15h, the examiner inputs a stop operation to the monitor 7 upon receiving a signal from the subject, or When the subject directly operates the operation switch 29 and inputs a stop operation, the stop operation receiving unit 52c receives a stop operation of the moving process.

  When the stop operation receiving unit 52c receives the stop operation, the stop control unit 52d stops the moving process of the focusing lens 15h by controlling the drive control unit 42 to stop driving the interlocking movement mechanism 27. Further, the stop control unit 52d detects a stop position which is a lens position of the focusing lens 15h stopped on the optical axis O2, and outputs information on the stop position to a focus position determination unit 54 described later. The stop position of the focusing lens 15h can be detected by various known methods such as detection using various position detection sensors or detection from the count value of the number of rotations of the motor of the interlocking movement mechanism 27.

  When the light flux of the optotype chart 26 having a high visual acuity value (for example, “1.0”) is projected on the fundus oculi Ef, the moving process of the focusing lens 15h may be continued depending on the state of the subject's eye E. The eye chart 26 may not be recognized by the eye E. Therefore, when the movement amount or the movement time of the focusing lens 15h exceeds the predetermined upper limit, the stop control unit 52d controls the drive control unit 42 to stop the movement processing of the focusing lens 15h. The detection of the stop position of the focusing lens 15h is not executed.

  The repetition control unit 52e projects the light flux of the optotype chart 26 corresponding to the new visual acuity value onto the fundus Ef from the optotype projection optical system 15 each time the optotype switching operation is input to the monitor 7. Every time the operation is performed, the movement control unit 52b, the stop operation receiving unit 52c, and the stop control unit 52d are repeatedly operated. Thereby, the movement processing of the focusing lens 15h for the second and subsequent times by the movement control unit 52b, the reception of the stop operation by the stop operation reception unit 52c, and the stop control of the movement processing by the stop control unit 52d are repeatedly executed. .

  FIG. 5 is an explanatory diagram for describing the first movement processing, stop operation acceptance, and stop control by each unit of the subjective test control unit 52 corresponding to the optotype chart 26 of the visual acuity value “0.1”. . As shown by reference numeral VA in FIG. 5, when the measurement control unit 34 is switched to the re-measurement mode, the output control unit 52a controls the light source control unit 40 and the chart plate drive control unit 48 to control the visual acuity value “0.1”. The luminous flux of the optotype chart 26 is projected on the fundus oculi Ef. The focus lens 15h is moved to the initial position (+ 1.5D) by the control of the drive control unit 42 (the interlocking movement mechanism 27) by the movement control unit 52b. Hereinafter, these states are referred to as “initial states”. In the initial state, the subject's eye E is in a cloudy fog state, so that the subject's eye E cannot recognize the optotype chart 26 with the visual acuity value “0.1”.

  When the eye to be inspected E is a hyperopic eye, the initial position of the focusing lens 15h is set further on the positive [D] side than + 1.5D.

  When the optotype chart 26 and the focusing lens 15h are set to the initial state, the movement controller 52b drives the interlocking movement mechanism 27 via the drive controller 42 to move the focusing lens 15h from the initial position to the optical axis O2. A first movement process of moving in the minus [D] direction along is started. Further, in conjunction with the movement of the focusing lens 15h, the reflex measurement unit 16a and the focusing lens 17d are integrally moved in the minus [D] direction by the interlocking movement mechanism 27.

  As shown by the reference sign VB in FIG. 5, when the moving process of the focusing lens 15h in the minus [D] direction is continued, the eye E is displayed on the optotype chart 26 with the visual acuity value “0.1” at some point. Can be recognized subjectively. When the eye E recognizes the optotype chart 26, the examiner inputs a stop operation to the monitor 7 by a signal from the examinee, or the examinee inputs a stop operation to the operation switch 29. By doing so, the stop operation receiving unit 52c receives the first stop operation of the moving process.

  Next, the stop control unit 52d controls the drive control unit 42 to stop driving the interlocking movement mechanism 27, thereby stopping the first movement processing of the focusing lens 15h. Further, the stop control unit 52d detects the stop position (+1.25 D in the present embodiment) of the focusing lens 15h, and outputs information on the stop position to the focus position determination unit 54. Thus, the first movement processing corresponding to the optotype chart 26 with the visual acuity value “0.1” is completed.

  FIG. 6 is an explanatory diagram for explaining the second movement processing, stop operation reception, and stop control by each unit of the subjective test control unit 52 corresponding to the optotype chart 26 with the visual acuity value “0.2”. . When the first movement processing is completed, the examiner inputs an optotype switching operation to the monitor 7. Accordingly, the emission control unit 52a drives the chart plate driving mechanism 20 via the chart plate drive control unit 48, and projects the light flux of the optotype chart 26 having the visual acuity value "0.2" onto the fundus oculi Ef. Next, the repetition control unit 52e repeatedly operates the movement control unit 52b, the stop operation reception unit 52c, and the stop control unit 52d.

  As indicated by reference numeral VIA in FIG. 6, the movement control unit 52b drives the interlocking movement mechanism 27 via the drive control unit 42 to move the focusing lens 15h from the previous (first) stop position (+ 1.25D). A second movement process for moving in the minus [D] direction along the optical axis O2 is started. In conjunction with the movement of the focusing lens 15h, the reflex measuring unit 16a and the focusing lens 17d are also moved integrally in the minus [D] direction by the interlocking movement mechanism 27.

  As shown by the reference numeral VIB in FIG. 6, when the moving process of the focusing lens 15h in the minus [D] direction is continued, the eye to be inspected E displays the optotype chart 26 with the visual acuity value “0.2” at some point. Can be recognized subjectively. When the eye E recognizes the optotype chart 26, the stop operation receiving unit 52c receives a stop operation of the second movement process in response to the stop operation by the examiner or the subject, and the stop control unit 52d drives the drive control unit. The second movement processing is stopped by stopping the driving of the interlocking movement mechanism 27 via 42. Then, the stop control unit 52d detects the stop position (+ 1.00D in this embodiment) of the focusing lens 15h, and outputs information on the stop position to the focus position determination unit 54. Thus, the second movement process corresponding to the optotype chart 26 having the visual acuity value “0.2” is completed.

  Similarly, every time the optotype switching operation is input to the monitor 7, the projection of the luminous flux of the optotype chart 26 having a higher visual acuity value than the previous time to the fundus oculi Ef, the movement processing of the focusing lens 15h, and the stop Acceptance of the operation and detection of the stop of the movement process and the stop position are repeatedly executed.

  FIG. 7 shows the focusing lens 15h after the fifth movement process, the stop operation acceptance, and the stop control are completed by each unit of the subjective test control unit 52 corresponding to the optotype chart 26 of the visual acuity value "0.8". FIG. 4 is an explanatory diagram for explaining a lens position of FIG. As shown in FIG. 7, by executing the fifth movement process, the stop operation reception, and the stop control in a state where the luminous flux of the optotype chart 26 having the visual acuity value “0.8” is projected on the fundus oculi Ef, For example, in the present embodiment, the stop position of the focusing lens 15h moves to + 0.25D.

  In this way, as the light flux of the optotype chart 26 having a higher visual acuity value than the previous time is projected onto the fundus oculi Ef, that is, as the visual acuity value of the optotype chart 26 presented to the eye E becomes higher, The stop position of the focusing lens 15h moves toward the subject's eye E (minus [D] direction).

  At this time, in conjunction with the movement of the focusing lens 15h by the interlocking movement mechanism 27, the reflex measurement unit 16a and the focusing lens 17d are also integrally moved to the eye E side. For this reason, when the focusing lens 15h is located at or near a stop position corresponding to the optotype chart 26 having a high visual acuity value (for example, a visual acuity value of "0.8" or more), the focusing lens 15h and the reflex measurement All of the unit 16a and the focusing lens 17d are set at a focusing position with respect to the eye E or at a position near the focusing position. As a result, as the focus of the luminous flux of the optotype chart 26 coincides with the fundus oculi Ef (including approximately coincidence, the same applies hereinafter), the luminous flux of the measurement pattern projected onto the fundus oculi Ef from the measurement pattern projection optical system 16 The focus can be made coincident with the fundus oculi Ef. Thereby, as shown in FIG. 14 described above, the ring image 24 is detected from the captured image 23 with a size suitable for the calculation of the eye refractive power, that is, the ring image 24 is detected within the range of the scale 100.

  Returning to FIG. 4, the focusing position determination unit 54 focuses the light beam of the optotype chart 26 on the fundus oculi Ef based on the detection result of the stop position for each of the optotype charts 26d by the stop control unit 52d. Is determined on the optical axis O2 (estimated value). As described above, since the focusing lens 15h, the reflex measurement unit 16a, and the focusing lens 17d move in conjunction with each other by the interlocking movement mechanism 27, the focusing position of the focusing lens 15h determines the light flux of the measurement pattern. The in-focus position (estimated position) of the reflex measurement unit 16a for focusing on the fundus oculi Ef and the in-focus position (estimated value) of the focusing lens 17d corresponding thereto are shown.

  FIG. 8 is an explanatory diagram for explaining a method of determining the focus position of the focusing lens 15h by the focus position determination unit 54. As shown in FIG. 8, the focus position determination unit 54 determines the type (visual acuity value) of the optotype chart 26 and the stop position (lens position) based on the detection result of the stop position for each optotype chart 26 by the stop control unit 52d. ) Is generated. Then, the focusing position determination unit 54 determines the focusing position of the focusing lens 15h based on the correspondence information 60 by the following first or second determination method. Although the correspondence information 60 is graphed in FIG. 8, it may be represented in another format. In FIG. 8, the description will be made on the assumption that the optotype chart 26 of the visual acuity value “1.0” is not recognized by the eye E.

  When the first determination method is selected, the focus position determination unit 54 determines, based on the correspondence information 60, the stop position corresponding to the optotype chart 26 having the highest visual acuity value among the stop positions (see the arrow A1 in the drawing). ), That is, the stop position (+ 0.25D) corresponding to the optotype chart 26 with the visual acuity value “0.8” is determined as the focus position of the focus lens 15h.

  In addition, when the second determination method is selected, the focus position determination unit 54 corresponds to the optotype chart 26 with a visual acuity value (for example, “1.0”) equal to or greater than a predetermined reference value based on the correspondence information 60. An estimated stop position (see the arrow A2 in the figure) as a stop position is calculated using a known fitting method such as a least squares method, and the estimated stop position is determined as a focus position of the focusing lens 15h.

  Then, the focus position determination unit 54 outputs the result of determining the focus position of the focusing lens 15h determined by the first determination method or the second determination method to the positioning control unit 56.

  Returning to FIG. 4, the positioning control unit 56 drives the interlocking movement mechanism 27 via the drive control unit 42 based on the determination result of the focus position of the focusing lens 15 h input from the focus position determination unit 54. Then, the focusing lens 15h is positioned at the focusing position. Thereby, the reflex measurement unit 16a is positioned at or near the in-focus position for the eye E on the optical axis O3, and the focusing lens 17d is at or near the in-focus position for the eye E on the optical axis O4. Is positioned. As a result, the reflex measurement unit 16a and the focusing lens 17d can be positioned at the in-focus position for the eye E estimated from the subjective test.

  The objective measurement control unit 58 controls the components of the operation control unit 30 after the focusing lens 15h is positioned at the in-focus position, and controls the eye refractive power of the eye E in the objective measurement mode described above. Similarly to the objective measurement of the above, the transition of the eye E to the cloud fogging state, the projection of the luminous flux of the measurement pattern onto the fundus oculi Ef, and the imaging of the fundus reflection light of the measurement pattern by the image sensor 12g are executed. Thereby, the captured image data of the captured image 23 is output from the imaging element 12g to the eye characteristic calculation unit 36, and the eye characteristic calculation unit 36 calculates the eye refractive power of the eye E to be inspected.

[Operation screen in re-measurement mode]
FIG. 9 is an explanatory diagram showing an example of the operation screen 25 displayed on the monitor 7 in the re-measurement mode. As shown in FIG. 9, the display control unit 46 causes the monitor 7 to display the operation screen 25 in the re-measurement mode. The operation screen 25 includes an observation image display area 62, a subjective examination display area 64, and a captured image display area 66.

  In the observation image display area 62, the observation image 22 of the anterior segment of the eye E is displayed. The display control unit 46 acquires the captured image data of the observation image 22 of the anterior eye part captured by the imaging element 12g in the re-measurement mode, and displays the observation image 22 in the observation image display area 62 based on the captured image data. . Then, the display control unit 46 updates the observation image 22 displayed in the observation image display area 62 every time image data of a new observation image 22 is captured by the imaging element 12g. Thus, the examiner can check the fixation state of the eye E to be examined.

  The subjective test display area 64 displays the status of the subjective test in the re-measurement mode. The subjective examination display area 64 includes an optotype display area 64a and a situation display area 64b.

  In the optotype display area 64a, the optotype chart 26 presented to the subject's eye E in the subjective test in the re-measurement mode is displayed. The display control unit 46 acquires information about the type of the optotype chart 26 inserted into the optical path 15q from the above-described emission control unit 52a, and displays the image of the optotype chart 26 in the optical path 15q in the optotype display area. 64a. Thus, the examiner can check the optotype chart 26 presented to the eye E.

  The status display area 64b includes a lens position display bar 70, an inspection result screen 72, and an icon 74 for display switching.

  The lens position display bar 70 indicates the lens position of the focusing lens 15h during the movement processing. The display controller 46 moves the focusing lens 15h on the optical axis O2 based on the detection result of the position detection sensor (not shown) described above or the count result of the count value of the number of rotations of the motor of the interlocking movement mechanism 27. Is obtained, and a lens position display bar 70 representing the lens position in a bar display format is displayed in the status display area 64b. Then, the display control unit 46 moves the cursor 70a of the lens position display bar 70 indicating the lens position according to a change in the lens position of the focusing lens 15h on the optical axis O2. Thus, the examiner can determine the lens position of the focusing lens 15h.

  The test result screen 72 shows a stop position for each of the optotype charts 26 having different visual acuity values. The display control unit 46 generates an inspection result screen 72 based on the detection result of the stop position for each of the optotype charts 26 detected by the stop control unit 52d, and displays the screen on the status display area 64b. In addition, the display control unit 46 determines the type (visual acuity value) of the optotype chart 26 presented to the subject based on the information on the type of the optotype chart 26 inserted into the optical path 15q described above. Is displayed so that it can be identified. Thus, the examiner can determine the stop position for each of the optotype charts 26.

  The icon 74 is operated when the display of the status display area 64b is alternately switched between the lens position display bar 70 and the inspection result screen 72 and the above-described correspondence information 60 (graph) shown in FIG. When the icon 74 is operated by the examiner while the lens position display bar 70 and the inspection result screen 72 are displayed in the status display area 64b, the display control unit 46 generates the focus position determination unit 54 described above. Based on the corresponding information 60, a graph of the corresponding information 60 is displayed in the status display area 64b. When the icon 74 is operated again by the examiner, the display controller 46 returns the display of the status display area 64b to the original lens position display bar 70 and the inspection result screen 72.

  In the captured image display area 66, a captured image 23 (ring image 24) captured by the image sensor 12g in objective measurement of the eye refractive power of the eye E is displayed. The display control unit 46 acquires captured image data of the captured image 23 captured by the image sensor 12g during the objective measurement in the re-measurement mode, and displays the captured image 23 in the captured image display area 66 based on the captured image data. . Further, the display control unit 46 sets the scales 100 and 100a serving as indices indicating the size of the ring image 24 suitable for the calculation of the eye refractive power in the captured image display area 66 as shown in FIG. The image is superimposed on the captured image 23. By displaying the captured image 23 in the captured image display area 66, the examiner can determine whether the ring image 24 exists in the captured image 23 and determine whether the ring image 24 has a size suitable for calculating the eye refractive power. You can check whether there is.

[Operation of Ophthalmic Device of Present Embodiment]
FIG. 10 shows the flow of the objective measurement processing of the eye refractive power of the eye E to be inspected by the ophthalmologic apparatus 1 having the above-described configuration, particularly the measurement processing of the eye refractive power in the re-measurement mode (corresponding to the operation method of the ophthalmologic apparatus of the present invention). It is a flowchart which shows a flow. In addition, since the measurement processing of the eye refractive power of the eye E in the objective measurement mode is a known technique, a specific description thereof is omitted here.

  As shown in FIG. 10, the luminous flux of the measurement pattern emitted from the measurement pattern projection optical system 16 is shifted from the fundus oculi Ef due to the disease of the eye E, or the ring image 24 is detected from the captured image 23. If it is impossible, it becomes impossible to measure the eye refractive power of the eye E in the objective measurement mode (step S1). In this case, the examiner inputs a mode switching operation to the re-measurement mode on the monitor 7 of the touch panel type. Then, in response to the mode switching operation on the monitor 7, the measurement control unit 34 switches the measurement mode to the re-measurement mode (step S2).

  When the measurement control unit 34 is switched to the re-measurement mode, each unit of the subjective test control unit 52 operates to determine the focus position of the focusing lens 15h that focuses the light flux of the target on the fundus oculi Ef. A subjective test is started (step S3).

  First, the control of the light source control unit 40 and the chart plate drive control unit 48 by the emission control unit 52a and the control of the drive control unit 42 by the movement control unit 52b bring the optotype chart 26 and the focusing lens 15h into the initial state. It is set (step S4). Thereby, the luminous flux of the optotype chart 26 having the visual acuity value "0.1" is projected onto the fundus oculi Ef, and the focusing lens 15h is moved to the initial position (+ 1.5D) on the optical axis O2.

  Next, as shown in FIG. 5 described above, the movement control unit 52b drives the interlocking movement mechanism 27 via the drive control unit 42 to move the focusing lens 15h from the initial position in the minus direction along the optical axis O2. The first movement processing for moving in the [D] direction is started (step S5, corresponding to the movement control step of the present invention).

  When the first movement processing is started, the eye E can subjectively recognize the optotype chart 26 with the visual acuity value “0.1” at some point. For this reason, as described with reference to FIG. 5 described above, the input of the stop operation to the monitor 7 or the operation switch 29 and the reception of the stop operation by the stop operation receiving unit 52c (step S6, the stop operation receiving process of the present invention) And the stop control unit 52d stops the movement processing (step S7, corresponding to the stop control step of the present invention). Further, the stop control unit 52d detects the stop position of the focusing lens 15h, and outputs information on the stop position to the focus position determination unit 54. Thus, the first movement processing corresponding to the optotype chart 26 with the visual acuity value “0.1” is completed.

  When the first movement processing is completed, the examiner inputs an optotype switching operation to the monitor 7. In response to this operation, the emission control unit 52a drives the chart plate drive mechanism 20 via the chart plate drive control unit 48 to project the light flux of the optotype chart 26 with the visual acuity value "0.2" onto the fundus Ef. (Step S8).

  Next, the movement control unit 52b drives the interlocking movement mechanism 27 via the drive control unit 42 to move the focusing lens 15h from the first stop position to the optical axis O2 as shown in FIG. A second movement process of moving the object along the minus [D] direction is started (step S5).

  When the second movement process is started, the eye E can subjectively recognize the optotype chart 26 with the visual acuity value “0.2” at some point. As a result, the processes of steps S6 and S7 described above are repeatedly executed (see FIG. 6). In step S7, the stop control unit 52d executes detection of the stop position of the focusing lens 15h and output of information on the stop position to the focus position determination unit 54. Thus, the second movement process corresponding to the optotype chart 26 having the visual acuity value “0.2” is completed.

  Similarly, every time the optotype switching operation is input to the monitor 7, the above-described processing from step S5 to step S7 is repeatedly executed. Then, when the sixth movement process corresponding to the optotype chart 26 with the visual acuity value "1.0" is completed, the subjective test of the eye E is completed (NO in step S8, step S9).

  When the subjective test is completed, the in-focus position determination unit 54 generates the above-described correspondence information 60 shown in FIG. 8 based on the detection result of the stop position for each of the optotype charts 26, and further, based on this correspondence information 60, The in-focus position of the focusing lens 15h is determined by the above-described first determination method or second determination method (step S10, corresponding to a focus position determination step of the present invention). Then, the focus position determining unit 54 outputs the result of determining the focus position of the focusing lens 15h to the positioning control unit 56.

  Next, the positioning control unit 56 receives the determination result from the focus position determination unit 54, drives the interlocking movement mechanism 27 via the drive control unit 42, and positions the focus lens 15h at the focus position. (Step S11, corresponding to the positioning control step of the present invention). Accordingly, in conjunction with the positioning of the focusing lens 15h, the reflex measurement unit 16a and the focusing lens 17d are positioned at the focusing position for the eye E estimated from the subjective test.

  When the focusing lens 15h is positioned at the in-focus position, the objective measurement control unit 58 controls each unit of the operation control unit 30 to shift the eye E to the cloud fogging state and measure the fundus Ef. The projection of the luminous flux of the pattern and the imaging of the fundus reflection light by the imaging element 12g are executed (step S12, corresponding to the objective measurement control step of the present invention). As a result, captured image data of the captured image 23 is output from the imaging element 12g to the eye characteristic calculation unit 36.

  FIG. 11 is an explanatory diagram for explaining a captured image 23 (ring image 24) acquired in the re-measurement mode. As shown by reference numeral XIA in FIG. 11, in a normal objective measurement mode, when a disease occurs in the eye E, the ring image 24 cannot be detected from the captured image 23, or the ring image 24 is omitted from the drawing. The image 24 may not fit inside the scale 100.

  On the other hand, in the re-measurement mode, the focusing lens 15h is positioned at the focusing position determined by the subjective examination of the eye E to be examined, so that the luminous flux of the measurement pattern projected from the measurement pattern projection optical system 16 to the fundus oculi Ef The position of the reflex measurement unit 16a and the focusing lens 17d is adjusted via the interlocking movement mechanism 27 so that the focal point of the lens coincides with the fundus Ef. As a result, as shown by reference numeral XIB in FIG. 11, the ring image 24 can be detected from the captured image 23 with a size suitable for calculating the eye refractive power, that is, the ring image 24 can be detected within the range of the scale 100. .

  Returning to FIG. 10, the eye characteristic calculation unit 36 analyzes the captured image data of the captured image 23 input from the image sensor 12g by a known method, and calculates the eye refractive power of the eye E to be inspected (Step S13). The calculation result of the eye refractive power by the eye characteristic calculating unit 36 is stored in a storage unit (not shown) as a measurement result of the eye refractive power of the eye E to be examined, and is displayed on the monitor 7 by the display control unit 46.

  The calculation result of the eye refractive power of the eye E calculated by the eye characteristic calculation unit 36 is used for a subjective test by another device. In addition, when the objective measurement of the eye refractive power of the eye E to be examined cannot be performed even in the re-measurement mode, a subjective test is performed by another device based on the correspondence information 60 described above.

[Effects of the present embodiment]
As described above, in the present embodiment, when it is not possible to objectively measure the eye refractive power of the eye E with a disease, a subjective test of the eye E is performed, and the focusing lens 15h for the eye E is executed. And the in-focus position (estimated position) of the reflex measurement unit 16a is determined. Objective measurement of eye refractive power is performed with the focusing lens 15h, the reflex measurement unit 16a, and the focusing lens 17d positioned at the determined positions. Try again. As a result, the ring image 24 can be detected from the captured image 23 with a size suitable for calculating the eye refractive power. Thus, the eye refractive power of the eye E with the disease can be measured.

[Ophthalmic apparatus of another embodiment 1]
FIG. 12 is a schematic diagram of an ophthalmologic apparatus 1A according to another embodiment. The ophthalmologic apparatus 1 of the above embodiment includes one measurement head 5 (optical system 8) corresponding to the eye E (one eye) to be examined, but the ophthalmologic apparatus 1A of another embodiment includes a pair of measurement heads corresponding to both eyes. A head 5 (optical system 8) is provided. The ophthalmologic apparatus 1A has basically the same configuration as the ophthalmologic apparatus 1 of the above embodiment, except that the ophthalmologic apparatus 1A includes a pair of measurement heads 5R and 5L provided on the table 80 and a pair of mirrors 82R and 82L. is there. Therefore, the same reference numerals are given to those having the same functions or configurations as those of the above-described embodiment, and the description thereof will be omitted.

  As shown in FIG. 12, the pair of measuring heads 5R, 5L and the pair of mirrors 82R, 82L are provided so as to be rotatable about axes perpendicular to the upper surface of the table 80. The pair of measuring heads 5R and 5L have the same configuration as the measuring head 5 of the above embodiment.

  The mirror 82R reflects the various light beams emitted from the measurement head 5R toward the eye E (right eye), and measures the reflected light of the various light beams reflected by the eye E (right eye). The light is reflected toward the head 5R. The mirror 82L reflects the various light beams emitted from the measurement head 5L toward the eye E (left eye), and reflects the various light beams reflected by the eye E (left eye). Is reflected toward the measurement head 5L. Thereby, objective measurement of the eye refractive power (acquisition of the captured image 23) of the eye E (right eye) is performed by the measurement head 5R, and the eye refractive power of the eye E (left eye) is measured by the measurement head 5L. Objective measurement (acquisition of the captured image 23) can be performed. As a result, the control unit 9 can calculate the eye refractive power of both eyes.

  At this time, the objective measurement of the eye refractive power of the eye E (right eye) by the measurement head 5R and the objective measurement of the eye refractive power of the eye E (left eye) by the measurement head 5L are performed simultaneously. Can not. Therefore, when the objective measurement of the eye refractive power of the eye E (right eye) to be examined is performed, the optotype projection optical system 15 of the measurement head 5L includes only the luminous flux of the background of the optotype (fixation target, optotype chart 26). To the left eye. The background of the optotype is, for example, a black frame surrounding the Randle ring in the case of the optotype chart 26 shown in FIGS. Conversely, when objective measurement of the eye refractive power of the eye E (left eye) is performed, the optotype projection optical system 15 of the measurement head 5R projects only the luminous flux of the optotype background to the right eye. Thereby, the fixation of both eyes can be stabilized.

[Ophthalmic apparatus of another embodiment 2]
FIG. 13 is a schematic diagram of the optotype projection optical system 15, the measurement pattern projection optical system 16, and the light receiving optical system 17 of the ophthalmologic apparatus 1B according to the second embodiment. The optotype projection optical system 15 of the ophthalmologic apparatus 1 of the above embodiment emits a light beam of an optotype (fixation target, optotype chart 26) from the LED light source 15a, the color correction filter 15b, and the collimator lens 15c, and emits light. By moving the focusing lens 15h back and forth on the axis O2, the presentation distance of the optotype to the eye E is changed.

  On the other hand, as shown in FIG. 13, the optotype projection optical system 15 of the ophthalmologic apparatus 1 </ b> B of the second embodiment includes an LED light source 15 a, a color correction filter 15 b, a collimator lens 15 c, and a focusing lens 15 h. And a target light beam emitting unit 15S (corresponding to a first light beam emitting unit of the present invention) arranged on the optical axis O2. The ophthalmologic apparatus 1 </ b> B of the second embodiment has basically the same configuration as the ophthalmologic apparatus 1 of the above-described embodiment, except that the ophthalmologic apparatus 1 </ b> B includes a target light beam emitting unit 15 </ b> S. Therefore, the same reference numerals are given to those having the same functions or configurations as those of the above-described embodiment, and the description thereof will be omitted.

  The target light beam emitting unit 15S includes an LED light source 15t, a diffusion plate 15u, a filter 15v such as an ND filter and a color correction filter, a collimator lens 15w, and a target 15x. The LED light source 15t emits white light toward the diffusion plate 15u. Thereby, the white light is diffused by the diffusion plate 15u, subjected to various processes by the filter 15v, further converted into a parallel light beam by the collimator lens 15w, and then enters the target unit 15x.

  As the optotype unit 15x, the chart plate 15d described in the above embodiment or a transmissive LCD or the like capable of displaying an arbitrary optotype is used. The optotype unit 15x transmits a parallel light beam of white light incident from the collimator lens 15w, and emits a light beam of the optotype (fixation target, optotype chart 26). Thereby, the light flux of the target is projected on the fundus oculi Ef as in the above embodiment.

  The optotype luminous flux emitting section 15S is arranged to be able to advance and retreat along the optical axis O2. For this reason, the optotype luminous flux emitting section 15S corresponds to “one side” of the present invention. Therefore, in the second embodiment, the presenting distance of the optotype with respect to the eye E can be changed by moving the optotype light emitting section 15S forward and backward along the optical axis O2 by the interlocking movement mechanism 27.

  The interlocking movement mechanism 27 of the second embodiment moves the optotype light beam emitting unit 15S, the reflex measurement unit 16a, and the focusing lens 17d in a direction (Z-axis direction) parallel to the optical axes O2 to O4. Let it. For this reason, the second embodiment is basically the same as the above embodiment except that the “target light beam emitting unit 15S” is moved by the interlocking movement mechanism 27 instead of moving the “focusing lens 15h” of the above embodiment. And the same effects as in the above embodiment can be obtained.

[Others]
In each of the above embodiments, in the subjective test in the re-measurement mode, the moving process of the focusing lens 15h (the target light beam emitting unit 15S) is repeatedly performed six times corresponding to the six types of the target charts 26. The number of repetitions of the process (the number of types of the target chart 26) is not particularly limited. For example, when it is assumed that the eyesight value of the eye E is high, the movement processing is performed in a state where the optotype chart 26 of the eyesight value “1.0” or “0.8” is presented to the eye E from the beginning. And the movement process may be completed once or twice.

  In the above embodiments, the ring-shaped measurement pattern is projected from the measurement pattern projection optical system 16 to the fundus oculi Ef, but the point-shaped measurement pattern is projected from the measurement pattern projection optical system 16 to the fundus oculi Ef. The light may be projected and the ring-shaped fundus reflected light may be received by the light receiving optical system 17. That is, the shape of the measurement pattern is not particularly limited as long as the ring-shaped fundus reflected light can be received by the light receiving optical system 17.

  In the above embodiments, the case where the optical axes O2 to O4 are parallel to each other has been described, but the optical axes O2 to O4 do not have to be parallel to each other. In this case, the interlocking moving mechanism 27 includes a moving mechanism (a motor driving mechanism or the like) that individually moves the focusing lens 15h, the reflex measurement unit 16a, and the focusing lens 17d, and an interlocking mechanism that drives the respective moving mechanisms in conjunction with each other. A drive control unit (such as a processor). Thus, even if the optical axes O2 to O4 are non-parallel, the focusing lens 15h, the reflex measurement unit 16a, and the focusing lens 17d are linked by the same amount of movement in the direction approaching or moving away from the eye E. Can be moved.

  In each of the above embodiments, the control device 9 is incorporated in the ophthalmologic devices 1, 1A, 1B. However, the control device 9 is provided with an arithmetic device (a personal computer, a portable terminal, or the like) separate from the ophthalmic devices 1, 1A, 1B. ) May be incorporated. That is, a processor or the like of the arithmetic device may function as the control device 9.

  In each of the above embodiments, the ophthalmologic apparatuses 1, 1A, and 1B that measure the eye refractive power as the eye characteristics of the eye E have been described as an example. However, the ring image 24 included in various captured images of the eye E is image-formed. The present invention is also applicable to an ophthalmologic apparatus that analyzes and measures various eye characteristics other than the eye refractive power of the eye E to be examined.

1, 1A, 1B ... ophthalmic device,
7 ... Monitor,
8 Optical system,
9 ... Control device,
12. Observation optical system,
12g ... image sensor,
15 ... Target target optical system,
15d ... Chart board,
15h ... Focusing lens,
15S: Optotype beam emitting portion,
16 ... measurement pattern projection optical system,
16a ... Ref measuring unit,
17 ... Reception optical system,
17d: Focusing lens,
22 ... observation image,
23 ... Captured image,
24 ... Ring image,
25 ... Operation screen,
26 ... Chart chart,
27 ... Interlocking movement mechanism,
30 ... operation control unit,
36 ... Eye characteristic calculation unit,
42 ... drive control unit,
48 ... Chart plate drive control unit,
52: subjective inspection control unit,
52a ... emission control unit,
52b ... movement control unit,
52c: Stop operation receiving unit,
52d: stop control unit,
52e ... repetition control unit,
54: Focusing position determining unit,
56 positioning control unit,
58: Objective measurement control unit

Claims (12)

An optotype projection optical system that has a first optical axis, projects a light beam of a target to the fundus of the eye to be examined, and a first light beam emitting unit that emits the light beam of the target, and a light beam of the target A target projection optical system having a first lens through which one of the first light beam emission unit and the first lens is disposed so as to be able to advance and retreat along the first optical axis;
A measurement pattern projecting optical system having a second optical axis, and projecting a light beam of the measurement pattern onto the fundus, wherein the second light beam emitting unit that emits the light beam of the measurement pattern includes the second light axis. A measurement pattern projection optical system that is arranged to be able to advance and retreat along
A light receiving optical system having a third optical axis, for receiving fundus reflected light of a light beam of the measurement pattern projected onto the fundus from the measurement pattern projection optical system, and along the third optical axis; A light receiving optical system having a second lens arranged to be movable forward and backward;
The one movement along the first optical axis, the movement of the second light beam emitting unit along the second optical axis, and the movement of the second lens along the third optical axis are performed in conjunction with each other. Interlocking movement mechanism,
Analyzing a ring image based on the fundus reflection light received by the light receiving optical system, an eye characteristic calculation unit that calculates eye characteristics of the subject's eye,
A movement control unit that controls the interlocking movement mechanism and executes a movement process of moving the one along the first optical axis;
During the execution of the movement process by the movement control unit, a stop operation receiving unit that receives a stop operation to stop the movement process at a position where the subject's eye subjectively recognized the optotype,
When the stop operation receiving unit receives the stop operation, a stop control unit that controls the interlocking movement mechanism to stop the moving process,
A focus position determining unit that determines the one focus position that focuses the light beam of the target on the fundus based on the one stop position stopped on the first optical axis by the stop control unit; ,
A positioning control unit that controls the interlocking movement mechanism and positions the one at the in-focus position determined by the in-focus position determination unit;
When the one is moved to the in-focus position, the projection of the light beam of the measurement pattern onto the eye to be inspected by the measurement pattern projection optical system, and the reception of the fundus reflection light by the light receiving optical system, Calculation of the eye characteristics by the eye characteristics calculation unit, and an objective measurement control unit that executes an objective measurement including:
An ophthalmologic apparatus comprising: The first light beam emitting unit can selectively emit light beams of a plurality of types of the optotypes having different visual acuity values,
An emission control unit that controls the first light flux emission unit to emit the light flux of the target in order by type of the target,
Each time a light beam of the optotype corresponding to the new visual acuity value is emitted from the first light beam emission unit, a repetition control unit that repeatedly operates the movement control unit, the stop operation reception unit, and the stop control unit. When,
With
The ophthalmologic apparatus according to claim 1, wherein the focus position determination unit determines the focus position based on the stop position for each type of the target.   The said focus position determination part determines the said stop position corresponding to the said optotype with the said highest visual acuity value among the said stop positions for every kind of the said optotype as the said in-focus position. Ophthalmic equipment.   The in-focus position determination unit calculates an estimated stop position that is the stop position corresponding to the target having the visual acuity value equal to or greater than a predetermined reference value, based on the stop position for each type of the target. The ophthalmologic apparatus according to claim 2, wherein the estimated stop position is determined as the focus position.   The ophthalmologic apparatus according to claim 4, wherein the in-focus position determination unit generates correspondence information indicating a correspondence between the type of the target and the stop position, and calculates the estimated stop position based on the correspondence information.   The ophthalmology according to any one of claims 2 to 5, wherein the emission control unit controls the first light flux emission unit to emit the light flux of the target in order from the target having the lower visual acuity value. apparatus.   The ophthalmologic apparatus according to claim 6, wherein the movement control unit controls the interlocking movement mechanism to move the one along the traveling direction of the light flux of the target.   When the movement control unit controls the interlocking movement mechanism to execute the first movement process, the one is moved along an advancing direction from an initial position at which the subject's eye is fogged, and The ophthalmologic apparatus according to claim 7, wherein when controlling the interlocking movement mechanism to execute the movement processing for the second time or later, the one is moved along the traveling direction from the previous stop position.   The ophthalmologic apparatus according to any one of claims 1 to 8, wherein the second light beam emitting unit emits a light beam of the ring-shaped measurement pattern.   The ophthalmology according to any one of claims 1 to 9, further comprising a pair of the optotype projection optical systems corresponding to both eyes, a pair of the measurement pattern projection optical systems, and a pair of the light receiving optical systems. apparatus.   The ophthalmologic apparatus according to any one of claims 1 to 10, wherein the first optical axis, the second optical axis, and the third optical axis are parallel to each other. An optotype projection optical system that has a first optical axis, projects a light beam of a target to the fundus of the eye to be examined, and a first light beam emitting unit that emits the light beam of the target, and a light beam of the target A target projection optical system having a first lens through which one of the first light beam emission unit and the first lens is disposed so as to be able to advance and retreat along the first optical axis;
A measurement pattern projecting optical system having a second optical axis, and projecting a light beam of the measurement pattern onto the fundus, wherein the second light beam emitting unit that emits the light beam of the measurement pattern includes the second light axis. A measurement pattern projection optical system that is arranged to be able to advance and retreat along
A light receiving optical system having a third optical axis, for receiving fundus reflected light of a light beam of the measurement pattern projected onto the fundus from the measurement pattern projection optical system, and along the third optical axis; A light receiving optical system having a second lens arranged to be movable forward and backward;
The one movement along the first optical axis, the movement of the second light beam emitting unit along the second optical axis, and the movement of the second lens along the third optical axis are performed in conjunction with each other. Interlocking movement mechanism,
Analyzing a ring image based on the fundus reflection light received by the light receiving optical system, an eye characteristic calculation unit that calculates eye characteristics of the subject's eye,
An operation method of an ophthalmologic apparatus including:
A movement control unit that controls the interlocking movement mechanism to perform a movement process of moving the one along the first optical axis;
A stop operation receiving unit that receives a stop operation that stops the moving process at a position where the subject's eye subjectively recognized the optotype during execution of the moving process by the movement control unit,
A stop control unit that, when the stop operation is received by the stop operation receiving unit, controls the interlocking movement mechanism to stop the moving process;
A focus position determination unit that determines the one focus position at which the light flux of the target is focused on the fundus based on the one stop position stopped on the first optical axis by the stop control unit. Focusing position determining step to be performed;
A positioning control unit that controls the interlocking movement mechanism to position the one at the in-focus position determined by the in-focus position determination unit;
In the objective measurement control step, when the one is moved to the in-focus position, the measurement pattern projection optical system projects the light beam of the measurement pattern onto the eye to be inspected by the measurement pattern projection optical system, and the light receiving optical system Receiving the fundus reflection light, and calculating the eye characteristics by the eye characteristics calculation unit, and performing an objective measurement control step of executing an objective measurement including:
An operation method of an ophthalmologic apparatus having:

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