JP2015139526A - Ophthalmologic apparatus and control method of ophthalmologic apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ophthalmologic apparatus capable of performing observation of an eye to be examined and positioning while switching a measurement mode.SOLUTION: An ophthalmologic apparatus includes: a base; an optometrical unit movable in a plurality of directions with respect to the base; a first optometry part contained in the optometrical unit, which includes an optical system for examining first eye characteristics of an eye to be examined; a second optometry part contained in the optometrical unit, which includes an optical system for examining second eye characteristics of the eye to be examined; a drive mechanism capable of driving the optometrical unit in a plurality of directions with respect to the base; and an observation unit capable of observing the eye to be examined, separately from the optometrical unit. While moving the optometrical unit with respect to the base by the drive mechanism for performing a second examination by the second optometry part after examining the eye to be examined using the first optometry part, the eye to be examined is observed by the observation unit, and positioning for the second optometry part is performed by the drive mechanism.

Description

  The present invention relates to an ophthalmologic apparatus capable of inspecting eye characteristics of an eye to be examined and a control method thereof.

  As an ophthalmologic apparatus that inspects a plurality of eye characteristics of an eye to be examined, a composite apparatus that includes different units and inspects different eye characteristics using each of these units is known. For example, Patent Document 1 discloses an intraocular pressure measurement in a composite apparatus having an intraocular pressure measurement unit that measures the intraocular pressure of a subject eye in a non-contact manner and an ocular refractive power measurement unit that measures an eye refractive power of the subject eye. And the one that switches between eye refractive power measurement are known (Patent Document 1).

JP 2007-144128 A JP 2008-245951 A

  In such an ophthalmologic apparatus for examining a plurality of eye characteristics, each of the intraocular pressure measurement unit and the eye refractive power measurement unit has a test eye observation unit, and before performing each measurement, alignment with the test eye, It is necessary to perform so-called alignment. However, in the case of the configuration disclosed in Patent Document 1, the eye to be examined cannot be observed while switching the measurement, for example, while switching from the intraocular pressure measurement to the eye refractive power measurement.

  On the other hand, in the ophthalmologic apparatus disclosed in Patent Document 2, during the switching of the measurement mode, the observation screen before switching and the observation screen after switching are simultaneously displayed in the display screen, thereby observing the state of the eye to be examined as much as possible. It is the structure which can perform (patent document 2). However, in the case of the configuration as described above, the eye to be examined during switching can be (limitedly) observed, but since the examination itself takes time, it is desirable to reduce the burden on the subject.

  The present invention has been made in view of the above circumstances, and provides an ophthalmologic apparatus capable of achieving both suitable observation of an eye to be examined and shortening of the time required for examination in an examination apparatus composed of a plurality of apparatuses. The purpose is to do.

In order to achieve the above object, an ophthalmologic apparatus according to the present invention comprises:
A base, an optometry unit movable in a plurality of directions with respect to the base, and a first optometry unit including an optical system included in the optometry unit for inspecting a first eye characteristic of the eye to be examined A second optometry unit included in the optometry unit and having an optical system for inspecting a second eye characteristic of the eye to be examined; and a drive mechanism capable of driving the optometry unit in a plurality of directions with respect to the base. In an ophthalmologic apparatus having an observation unit capable of observing an eye to be examined separately from the optometry unit, after examining the eye to be examined using the first optometry unit, the second optometry unit While the optometry unit is moved with respect to the base by the drive mechanism in order to perform the second examination, the eye to be examined is observed by the observation unit, and the second optometry unit is observed by the drive mechanism. It is characterized by performing alignment for.

In the ophthalmologic apparatus according to the present invention,
It is preferable that the observation unit is disposed in the device fixing portion.

Furthermore, in the ophthalmic apparatus according to the present invention,
The first optometry unit is preferably an optometry unit for examining eye refractive power and the shape of the cornea, and the second optometry unit is preferably an optometry unit for measuring intraocular pressure.

Alternatively, the ophthalmic apparatus according to the present invention is
The base,
An optometry unit movable in a plurality of directions with respect to the base;
A drive mechanism capable of driving the optometry unit in a plurality of directions with respect to the base;
Apart from the optometry unit, an observation unit capable of observing the eye to be examined;
In an ophthalmic device having
After inspecting one eye to be examined using the optometry unit, while moving the optometry unit with respect to the base by the drive mechanism to inspect the other eye, the observation unit Then, the eye to be examined is observed, and alignment for examining the other eye to be examined is performed by the drive mechanism.

  By using the ophthalmic apparatus as described above, it is possible to achieve both the appropriate observation of the eye to be examined and the reduction of the time required for the examination even for an ophthalmic apparatus that requires switching between measurement modes with different configurations. It becomes.

1 is a schematic configuration diagram of an ophthalmologic apparatus according to an embodiment of the present invention. It is an optical system block diagram of the optometry unit of the ophthalmologic apparatus which concerns on one Embodiment of this invention. FIG. 3 is a perspective view of an alignment prism diaphragm of the ophthalmic apparatus illustrated in FIG. 2. It is an optical system block diagram of the observation unit at the time of switching of the ophthalmologic apparatus concerning one embodiment of the present invention. FIG. 2 is a system block diagram of an electric circuit representing a control system of the ophthalmologic apparatus illustrated in FIG. 1. It is explanatory drawing of the anterior eye part image at the time of measurement obtained by the ophthalmologic apparatus shown in FIG. It is explanatory drawing of the anterior ocular segment image obtained at the time of the test | inspection switch of the ophthalmic apparatus which concerns on one Embodiment of this invention. It is a flowchart at the time of optometry of the ophthalmic apparatus which concerns on one Embodiment of this invention.

Embodiments of the present invention will be described below in detail with reference to the accompanying drawings.
FIG. 1 is a schematic configuration diagram of an ophthalmologic apparatus according to an embodiment of the present invention.

  The ophthalmologic apparatus includes a base 100, a face support unit 140 for supporting the subject's face, a driving unit 120 provided on the base 100, a joystick 101 as an operation member, a display unit 109, and a driving unit 120. And an optometry unit 110 attached to the.

  The driving means 120 has a driving mechanism corresponding to each axis so that the optometry unit 110 can move in a plurality of directions of X, Y, and Z with respect to the base 100 which is an apparatus fixing portion, that is, a base. . The drive mechanism can drive the optometry unit in order to align the optometry unit that actually performs the test with the left and right eyes, cornea, fundus, and the like to be inspected.

[X axis]
The X frame 102 is movable in the left-right direction with respect to the base 100 (a direction perpendicular to the paper surface of the drawing, hereinafter referred to as the X-axis direction). The drive mechanism in the X-axis direction can move in the X-axis direction on the X-axis drive motor 103 fixed on the base 100, a feed screw (not shown) connected to the output shaft of the motor, and the feed screw. It consists of a nut (not shown) fixed to the X frame 102. As the X-axis drive motor 103 rotates, the X frame 102 moves in the X-axis direction via a feed screw and a nut.

[Y axis]
The Y frame 106 is movable in the vertical direction (the vertical direction in the drawing, hereinafter referred to as the Y-axis direction) with respect to the X frame 102. The drive mechanism in the Y-axis direction is movable in the Y-axis direction on the Y-axis drive motor 104 fixed on the X frame 102, the Y-feed screw 105 connected to the output shaft of the motor, and the Y-feed screw 105 The Y nut 114 is fixed to the Y frame 106. As the Y-axis drive motor 104 rotates, the Y frame 106 moves in the Y-axis direction via the Y feed screw 105 and the Y nut 114.

[Z-axis]
The Z frame 107 is movable relative to the Y frame 106 in the front-rear direction (left-right direction in the drawing, hereinafter referred to as the Z-axis direction). The drive mechanism in the Z-axis direction is movable in the Z-axis direction on the Z-axis drive motor 108 fixed on the Z frame 107, the Z-feed screw 109 connected to the output shaft of the motor, and the Z-feed screw 109 And a Z nut 115 fixed to the Y frame 106. As the Z-axis drive motor 108 rotates, the Z frame 107 moves in the Z-axis direction via the Z feed screw 109 and the Z nut 115.

[LCD monitor]
At a position away from the examiner side end of the Z frame 107, an LCD monitor 109, which is a display member for observing the eye E to be examined, is fixed to a column embedded in the base 100.

[Face support unit]
The face support unit 140 is movable in the Y-axis direction and has a chin rest 112 and a face support frame 113. When performing an optometry, the subject places the chin on the chin rest 112 and presses the forehead against the forehead receiving portion of the face support frame 113, thereby fixing the position of the eye to be examined with respect to the base 100. it can.

[Joystick]
The base 100 is provided with a joystick 101, a measurement start button 121, and an optometry switch button 122, which are operation members for aligning the optometry unit 110 with the eye E to be examined. The examiner tilts the joystick 101 to instruct the driving direction, driving amount, and driving speed of the driving unit 120, and aligns the optometry unit 110 with the eye to be examined. Thereafter, the measurement start button 121 provided on the joystick 101 is pressed to measure the eye characteristics of the eye to be examined.

[Observation unit at switching]
The base 100 is provided with a switching observation unit 130 for observing the eye E when switching the measurement mode. The observation unit 130 is fixed to a support column that supports the LCD monitor 109 described above, and is fixed to the base 100 so that both eyes of the subject can be observed regardless of the position of the optometry unit 110.

  The switching observation unit 130 includes an image sensor 131 and an objective lens 132 as an optical system for measuring and observing the eye to be examined, as will be described later.

[Optical system]
FIG. 2 shows a configuration diagram of an optical system in the optometry unit 110 in the present embodiment.
The optical system in the optometry unit 110 includes a first optical system 200 and a second optical system 300. Here, the first optical system 200 is an optical system for inspecting the first eye characteristic of the eye to be examined in the present invention, and is exemplified as a first optometry unit included in the optometry unit 110. The second optical system 300 is an optical system for inspecting the second eye characteristic of the eye to be examined, and is exemplified as a second optometry unit included in the optometry unit 110.

[First optical system]
The first optical system 200 is an optical system for inspecting the eye refractive power of the eye to be examined.
On the optical path 01 from the eye refractive power measurement light source 201 that irradiates light having a wavelength of 880 nm to the eye E, a lens 202, a diaphragm 203, a perforated mirror 204, a diffusion plate 222, a lens 205, and a dichroic mirror 206 are sequentially provided. Has been placed. The diaphragm 203 is arranged almost conjugate with the pupil Ep of the eye E. The diffusing plate 222 can be inserted into and removed from the optical path 01 as will be described later. The dichroic mirror 206 totally reflects infrared and visible light having a wavelength of 880 nm or less from the eye E side, and partially reflects a light beam having a wavelength of 880 nm or more.

  On the optical path 02 in the reflection direction of the perforated mirror 204, a stop 207 having an annular slit substantially conjugate with the pupil Ep, a light beam splitting prism 208, a lens 209, and an image sensor 210 are sequentially arranged.

  The optical system described above is for eye refractive power measurement, and the light beam emitted from the measurement light source 201 is primarily imaged in front of the lens 205 by the lens 202 while the light beam is narrowed by the diaphragm 203. The light passes through the dichroic mirror 206 and is projected onto the center of the pupil of the eye E to be examined.

The reflected light of the projected light beam is incident on the lens 205 again through the center of the pupil. The incident light beam is reflected around the perforated mirror 204 after passing through the lens 205.
The reflected light beam is pupil-separated by a stop 207 and a light beam spectroscopic prism 208 that are substantially conjugate to the eye pupil Ep to be examined, and projected onto the light receiving surface of the image sensor 210 as a ring image.

If the eye E is a normal eye, the ring image is a predetermined circle. The myopic eye has a smaller circle than the normal eye, and the far-sighted eye has a larger circle and is projected.
When the subject eye E has astigmatism, the ring image becomes an ellipse, and the angle between the horizontal axis and the ellipse becomes the astigmatism axis angle. The refractive power is obtained based on the coefficient of the ellipse.

  On the other hand, in the reflection direction of the dichroic mirror 206, a fixation target projection optical system and an alignment light receiving optical system that shares anterior eye portion observation and alignment detection of the eye to be examined are arranged.

  On the optical path 03 of the fixation target projection optical system, a lens 211, a dichroic mirror 212, a lens 213, a folding mirror 214, a lens 215, a fixation target 216, and a fixation target illumination light source 217 are sequentially arranged. .

At the time of fixation fixation, the projected light flux from the fixation target illumination light source 217 illuminates the fixation target 216 from the back side, and the lens 215, the folding mirror 214, the lens 213, the dichroic mirror 212, the lens 211, and the dichroic. The light is projected onto the fundus Er of the eye E through the mirror 206.
The lens 215 can be moved in the optical axis direction by a fixation guidance motor 224 in order to guide the diopter of the eye E and realize a cloud state.

  On the optical path 04 in the reflection direction of the dichroic mirror 212, an alignment prism diaphragm 223, a lens 218, and an image sensor 220 that are inserted and removed by an alignment prism diaphragm insertion / extraction solenoid 411 (see FIG. 5) are sequentially arranged.

  By inserting / extracting the alignment prism diaphragm 223, alignment can be performed when the alignment prism diaphragm 223 is on the optical path 04, and anterior eye observation or transillumination observation can be performed when retracted from the optical path.

  Here, FIG. 3A shows the shape of the alignment prism diaphragm 223. Three openings 223a, 223b, and 223c are provided in the disc-shaped diaphragm. Alignment prisms 231a and 231b that transmit light beams only in the vicinity of a wavelength of 880 nm are attached to the dichroic mirror 212 side of the openings 223c and 223b on both sides.

  Returning to FIG. 2, anterior segment illumination light sources 221 a and 221 b having a wavelength of about 780 nm are disposed obliquely in front of the anterior segment of the eye E. The luminous flux of the anterior segment image of the eye E illuminated by the anterior segment illumination light sources 221a and 221b passes through the dichroic mirror 206, the lens 211, the dichroic mirror 212, and the central aperture 223a of the alignment prism diaphragm. An image is formed on the surface 220 of the light receiving sensor.

  A light source for alignment detection is also used as a measurement light source 201 for measuring eye refractive power. At the time of alignment, the translucent diffusion plate 222 is inserted into the optical path 01 by the diffusion plate insertion / removal solenoid 410.

  The position where the diffusion plate 222 is inserted is a substantially primary imaging position by the projection lens 202 of the measurement light source 201 described above, and is inserted at the focal position of the lens 205. As a result, the image of the measurement light source 201 is once formed on the diffusion plate 222 and becomes a secondary light source, and is projected from the lens 205 toward the eye E as a thick parallel light beam.

  This parallel light beam is reflected by the eye cornea Ef to be examined to form a bright spot image, and the light beam is again partially reflected by the dichroic mirror 206 and reflected by the dichroic mirror 212 via the lens 211. The parallel light flux further passes through the opening 223a of the alignment prism diaphragm and the alignment prisms 231a and 231b, is converged on the lens 218, and forms an image on the image sensor 220.

  As shown in FIG. 3A, the central opening 223a of the alignment prism diaphragm 223 is configured to allow a light beam having a wavelength of 780 nm or more of the anterior segment illumination light sources 221a and 221b to pass. Therefore, the reflected luminous flux of the anterior segment image illuminated by the anterior segment illumination light sources 221a and 221b follows the observation optical system in the same manner as the path of the reflected luminous flux of the cornea Ef, and passes through the opening 223a of the alignment prism diaphragm 223. The image is formed on the image sensor 220 by the imaging lens 218.

  Further, the light beam transmitted through the alignment prism 231a is refracted downward, and the light beam transmitted through the alignment prism 231b is refracted upward. The eye E can be aligned based on the positional relationship of the light flux through these diaphragms.

  On the other hand, in a state where the alignment prism diaphragm 223 is retracted from the optical path 04, a part of the light beam in the illuminated pupil region is reflected by the dichroic mirror 206 due to the reflected light beam on the fundus Er from the measurement light source 201. This reflected light beam is further reflected by the dichroic mirror 212 via the lens 211 and projected onto the image sensor 220 by the lens 218. The transillumination observation of the eye E can be performed with this light beam.

[Second optical system]
The second optical system 300 is an optical system for examining the intraocular pressure of the eye to be examined.
On the light receiving optical path and the alignment detecting optical path 06 of the observation optical system for the eye E, a parallel plane glass 301, an objective lens 302, an air chamber 323, an observation window 304, a dichroic mirror 305, a prism stop 306, and an imaging lens 307 are provided. , And the image sensor 308 are sequentially arranged. A nozzle 303 communicating with the air chamber 323 is disposed on the central axis of the flat glass 301 and the objective lens 302.
The plane-parallel glass 301 and the objective lens 302 are supported by an objective barrel 309, and external eye illumination light sources 310a and 310b for illuminating the eye E are disposed on the outside thereof.

  FIG. 3B shows the shape of the prism stop 306. Three openings 306a, 306b, and 306c are provided in the disc-shaped diaphragm. Alignment prisms 232a and 232b that transmit light beams only in the vicinity of a wavelength of 880 nm are attached to the dichroic mirror 305 side of the openings 306c and 306b on both sides.

  A relay lens 311, a half mirror 312, an aperture 313, and a light receiving element 314 are arranged in the reflection direction of the dichroic mirror 305 on the optical path 07 of the deformation detection light receiving optical system when the cornea Ef is deformed in the visual axis direction. Yes. Note that the aperture 313 is disposed at a position where a cornea reflection image of a measurement light source 317, which will be described later, becomes conjugate at the time of predetermined deformation.

The relay lens 311 is designed to form a corneal reflection image having a size substantially equal to that of the aperture 313 when the cornea Ec is deformed to a predetermined degree.
On the optical path 05 of the measurement light source projection optical system for measuring the deformation of the cornea Ef, a half mirror 315, a projection lens 316, and a measurement light source 317 are arranged in the incident direction of the half mirror 312. The measurement light source 317 is composed of a near-infrared LED that is used for both measurement and alignment with the eye E. Further, in the incident direction of the half mirror 315, a fixation light source 318 made of an LED fixed by the subject is arranged.

  In the air chamber 323, a piston 320 is fitted into an objective barrel 309 constituting a part thereof, and the piston 320 is driven by a solenoid 322. Note that a pressure sensor 324 for monitoring the internal pressure is disposed in the air chamber 323.

  The optometry unit 110 is configured to be able to switch between optometry by the first optical system 200 and optometry by the second optical system 300 by moving in the left-right direction (X-axis direction).

[Optical system for observation during switching]
FIG. 4 is a plan view of the observation unit 130 at the time of switching. The optical system of the switching observation unit 130 includes an image sensor 131 and an objective lens 132. As described above, the eyes E (L) and E (R) to be examined are arranged at positions where they can be observed simultaneously. The switching observation unit 130 corresponds to an observation unit capable of observing the eye to be examined separately from the optometry unit in the present invention, or an observation unit for observing an examination target while the optometry unit is being driven. In this embodiment, the observation unit is fixed to the base 100 independently of the optometry unit or the drive unit that drives the optometry unit. However, the function of the observation unit can be assigned to the first optometry unit or the second optometry unit described above.

[System block diagram]
FIG. 5 is a system block diagram. A system control unit 401 that controls the entire system includes a program storage unit, a data storage unit that stores data for correcting intraocular pressure values, eye refractive power values, and the like, and an input / output device that controls input / output with various devices. It has an output control unit and an arithmetic processing unit for calculating data obtained from various devices.

  The system control unit 401 includes a tilt angle input 402 when the measurement unit 110 is tilted back and forth and left and right, and an encoder input 403 when rotated, and a measurement start button. A measurement start button input 404 when pressed is connected. The operation panel 405 on the base 100 is provided with a print button, a chin rest up / down button, and the like, and a signal is notified to the system control unit 401 when the button is input. Further, various position sensors 406 including a positioning sensor notify the system control unit 401 of a signal when the sensors are turned on.

An anterior segment image of the eye E to be examined captured by the image sensor 220 is stored in the memory 408. A pupil and corneal reflection image of the eye E is extracted from the image stored in the memory 408, and alignment detection is performed. In addition, the anterior ocular segment image of the eye E imaged by the image sensor 220 is combined with character and graphic data, and an anterior ocular segment image, measurement values, and the like are displayed on the LCD monitor 109.
The eye refractive power calculation ring image photographed by the image sensor 210 is stored in the memory 408.
The anterior ocular segment images of the subject's eyes E (L) and E (R) imaged by the image sensor 131 are stored in the memory 408.

  The solenoids of the diffusion plate insertion / removal solenoid 410, the alignment prism diaphragm insertion / removal solenoid 411, and the solenoid 322 are driven and controlled by a command from the system control unit 401 via the solenoid drive circuit 409. In addition, the X-axis drive motor 103, the Y-axis drive motor 104, the Z-axis drive motor 108, the chin rest drive motor 116, the face support drive motor 131, and the fixation target induction motor 224 are connected to the system via the motor drive circuit 413. It is driven by a command from the control unit 401.

Eye refractive power measurement light source 201, external eye illumination light sources 221a and 221b for eye refractive power measurement, fixation target light source 217, intraocular pressure measurement light source 317, internal fixation light source 318, and external eye for intraocular pressure measurement The illumination light sources 310a and 310b control lighting, extinction, and light amount change by a command from the system control unit 401 via the light source driving circuit 412.
The operation of the apparatus having the above configuration will be described.

[Description of operation]
(Eye refractive power measurement)
As shown in FIG. 6A, at the time of alignment, the corneal bright spots formed by the cornea Ef are divided by the openings 223a, 223b, and 223c of the alignment prism diaphragm 223 and the prisms 231a and 231b. In addition, bright spot images 221a ′ and 221b ′ of the external illumination light sources 221a and 221b are also obtained from the eye E to be examined illuminated by the external illumination light sources 221a and 221b. The bright spot images obtained by the alignment prism diaphragm 233 are picked up as index images Ta, Tb, and Tc by the image sensor 220 together with the bright spot images of the external illumination light sources 221a and 221b.
Alignment is performed in two stages: rough alignment for rough alignment and fine alignment for precise alignment.

  The rough alignment uses the eye E and the bright spot images 221a 'and 221b' of the external illumination light sources 221a and 221b. When the eye E and the bright spot images 221a ′ and 221b ′ can be detected, the system control unit 401 controls the motor drive circuit 413 so that the bright spot images 221a ′ and 221b ′ are in the XY directions with respect to the pupil center of the eye E. The measurement unit 110 is driven in the vertical and horizontal directions so as to match. Next, the system control unit 401 calculates the Z coordinates and areas of the bright spot images 221a ′ and 221b ′, and further performs coarse alignment by driving the measurement unit 110 in the front-rear direction so as to align them with predetermined positions. .

  Index images Ta, Tb, and Tc are used for fine alignment. When the three bright spots Ta, Tb, and Tc can be detected, the system control unit 401 controls the motor drive circuit 413 to drive the measurement unit 110 in the vertical and horizontal directions so that the central bright spot Tc coincides with the central direction. . Next, the system control unit 401 further drives the measurement unit 110 in the front-rear direction so that the bright spots Ta and Tb are aligned in the vertical direction with respect to the bright spot Tc, so that the three corneal bright spots Ta, Tb, and Tc are 1 in the vertical direction. Complete alignment in line.

  In order to measure the eye refractive power, the system control unit 401 retracts the diffusion plate 222 inserted in the optical path 01 for auto-alignment from the optical path 01. The light quantity of the measurement light source 201 is adjusted, and the measurement light beam is projected onto the fundus Er of the eye E to be examined.

Reflected light from the fundus follows the optical path 02 and is received by the image sensor 210. The captured fundus image is projected in a ring shape by the ring diaphragm 207 by the refractive power of the eye to be examined. This ring image is stored in the memory 408.
The center-of-gravity coordinates of the ring image stored in the memory 408 are calculated, and an elliptic equation is obtained by a known method. The ocular refractive power of the eye E is calculated by calculating the obtained ellipse diameter, minor axis and inclination of the major axis.
The relationship between the obtained ellipse diameter, the eye refractive power value corresponding to the minor axis, and the angle of the ellipse axis on the light receiving surface of the image sensor 210 and the astigmatism axis is corrected in advance in the device manufacturing process. .

  In this way, the fixation target induction motor 224 is driven via the motor drive circuit 413 from the determined eye refractive power value to a position corresponding to the refractive power value, the lens 215 is moved, and the eye E The fixation target 216 is presented to the eye E with a refraction degree equivalent to the refraction degree.

  Thereafter, the lens 215 is moved away by a predetermined amount, the fixation target 216 is fogged, the measurement light source is turned on again, and the refractive power is measured. In this way, measurement of refractive power → cloud fog using the fixation target 216 → measurement of refractive power can be repeated to obtain a final measurement value in which the refractive power is stabilized.

(Intraocular pressure measurement)
As shown in FIG. 6B, at the time of alignment of tonometry, the corneal bright spots formed by the cornea Ef are the openings 306a, 306b, 306c and the prism 232a of the alignment prism diaphragm 306 shown in FIG. It is divided by H.232b. Further, bright spot images 310a ′ and 310b ′ of the external illumination light sources 310a and 310b are also obtained from the eye E to be examined illuminated by the external illumination light sources 310a and 310b. The bright spot images obtained by the alignment prism diaphragm 306 are picked up as index images Ta, Tb, and Tc by the image sensor 308 together with the bright spot images of the external illumination light sources 310a and 310b. The following is the same as the alignment for the eye refractive power measurement.

When the alignment is completed, an intraocular pressure measurement is performed. The system control unit 401 drives the solenoid 322, and the air in the air chamber 323 is compressed by the piston 320 pushed up by the solenoid 322, and is ejected from the nozzle 303 toward the cornea Ef of the eye E as pulsed air.
The pressure signal detected by the pressure sensor 324 of the air chamber 323 and the light reception signal from the light receiving element 314 are output to the system control unit 401, and the system control unit 401 calculates the intraocular pressure value from the peak value of the light reception signal and the pressure signal at that time. calculate.

(Rough alignment when switching measurement mode)
As an example, an operation when the measurement mode is switched from the eye refractive power measurement to the intraocular pressure measurement for the right eye E (R) will be described. Immediately after the completion of the measurement of the eye refractive power for the right eye E (R), the system control unit 401 receives the captured image of the right eye E (R) and the coordinate information of the optometry unit 110 from the imaging device 220 for observation during eye refractive power measurement. Stored in the memory 408.

  The system control unit 401 calculates the center position coordinates (Xa, Ya) of the pupil Ep (R) of the right eye from the captured image of the right eye E (R) before switching, which is stored in the memory 408. Further, it is necessary to switch to the intraocular pressure measurement mode from the difference between the calculated center coordinates (Xa, Ya) and the eye refractive power measurement optical axis center and the intraocular pressure measurement optical axis center stored in the memory 408 in advance. The coordinates (Xb, Yb) of the movement destination of the optometry unit are calculated.

  Next, the system control unit 401 controls the motor drive circuit 413, commands the movement amount of the optometry unit from the calculated coordinates, and drives the X-axis drive motor 103, the Y-axis drive motor 104, and the Z-axis drive motor 108. The optometry unit 110 is moved to a predetermined position where the intraocular pressure measurement is to be performed with respect to the right eye E (R). Simultaneously with the switching, the switching observation unit 130 starts observing the right eye E (R) and the left eye E (L) as shown in FIG. 7, and the display screen of the LCD monitor 109 is used for switching time observation. The image is switched from the image sensor 131.

  Of course, the observation unit 130 at the time of switching may start observation of the right eye E (R) and the left eye E (L) during the measurement of the eye refractive power. During measurement mode switching, fixation disparity of the subject's eye occurs due to various reasons such as looking away from the subject and fine fixation movement. In order to monitor the shift amount, the system control unit 401 receives a captured image of the pupil of the subject eye to be measured next from the image sensor 131, that is, the pupil Ep (R) of the right subject eye, and stores it in the memory 408. Store.

  In addition, the system control unit 401 calculates the center position coordinates (Xk, Yk) of the pupil Ep (R) of the right eye to be examined, which is stored in the memory 408, and the pupil center position coordinates of the right eye to be examined before the switching. The amounts of change ΔX = (Xa−Xk) and ΔY = (Ya−Yk) are calculated from the difference from (Xa, Ya). Further, the movement destination coordinates (Xb + ΔX, Yb + ΔY) to which the change amount is added are calculated.

  Next, the system control unit 401 controls the motor drive circuit 413 to instruct a movement amount up to the movement destination coordinates in consideration of the change amount, and drives the X-axis drive motor 103 and the Y-axis drive motor 104 to perform the right eye examination. Rough alignment of the optometry unit 110 is performed with respect to E (R). The system control unit 401 continues the rough alignment operation until the optometry unit 110 completes moving to the position where the right eye E (R) is to be subjected to intraocular pressure measurement.

  When the optometry unit 110 completes moving to the position where the right eye E (R) is to be subjected to intraocular pressure measurement, the display on the display monitor 109 is obtained from the image from the observation image sensor 131 at the time of switching from the imaging for observation at the time of intraocular pressure measurement. The image is switched from the element 308. By the alignment operation during the measurement mode switching, rough alignment of the optometry unit 110 with respect to the right eye E (R) is completed at the start of measurement of intraocular pressure.

  As described above, in the present embodiment, the system control unit 401 uses the first optical system 200 to inspect the eye to be inspected, and then performs a second inspection by the second optical system 300 using the drive mechanism as a base. The optometry unit 110 is moved with respect to 100. During this time, based on the image of the eye to be examined obtained by the observation unit 130 at the time of switching, it functions as a control unit that performs positioning for the second optical system 300 by the drive mechanism.

(Rough alignment when switching between left and right eye)
The same rough alignment can be performed not only when the measurement mode is switched, but also when the left and right eyes are switched in the same measurement mode. As a result, the measurement time can be further shortened.

  As an example, an operation when switching from the right eye E (R) to the left eye E (L) in the eye refractive power measurement mode will be described. Immediately after the completion of the measurement of the eye refractive power for the right eye E (R), the system control unit 401 uses the imaging image 131 for observation at the time of switching to pick up images of the right eye E (R) and the left eye E (L) and the optometry unit 110. Coordinate information is received and stored in the memory 408. The system control unit 401 stores the center position coordinates (Xra, Yra) of the pupil Ep (R) of the right eye based on the captured images of the right eye E (R) and the left eye E (L) before switching, which are stored in the memory 408. ) And the center position coordinates (Xla, Yla) of the pupil Ep (L) of the left eye to be examined.

  Next, the system control unit 401 controls the motor drive circuit 413 to drive the X-axis drive motor 103, the Y-axis drive motor 104, and the Z-axis drive motor 108 in order to perform the left / right switching of the eye to be examined. The left eye is moved to the pupil center coordinates (Xla, Yla). Simultaneously with the switching, the switching observation unit 130 starts observation of the left eye E (L) and the right eye E (R) as shown in FIG. 7, and the display screen of the LCD monitor 109 is for switching observation. The image is switched from the image sensor 131.

  Of course, the switching observation unit 130 may start observation of the left eye E (L) and the right eye E (R) during the measurement of the eye refractive power with respect to the right eye E (R). During the measurement mode switching, the system control unit 401 receives a captured image of the pupil of the eye to be examined next, that is, Ep (L), from the image sensor 131 and stores it in the memory 408.

  Further, the center position coordinates (Xlk, Ylk) of the pupil Ep (L) of the left eye to be examined during switching are calculated, and the difference from the center position coordinates (Xla, Yla) of the left eye E (L) before switching is calculated. The respective variations ΔX = (Xla−Xlk) and ΔY = (Yla−Ylk) are calculated. The system control unit 401 controls the motor drive circuit 413 to instruct the movement amount up to the movement destination coordinates in consideration of the change amount, and drives the X-axis drive motor 103, the Y-axis drive motor 104, and the Z-axis drive motor 108. The rough alignment of the optometry unit 110 is performed on the left eye E (L).

  The system control unit 401 continues the alignment operation until the optometry unit 110 completes the movement to the position where the eye refractive power measurement is performed on the left eye E (L). When the optometry unit 110 completes moving to the position for measuring the eye refractive power with respect to the left eye E (L), the display on the display monitor 109 is observed from the image from the imaging element 131 for observation at the time of switching. The image is switched from the image pickup device 220. By the alignment operation during the left / right switching of the eye to be examined, rough alignment of the optometry unit 110 with respect to the left eye E (L) is completed when the eye refractive power measurement of the left eye E (L) is started.

  As described above, in this embodiment, the system control unit 401 inspects one eye to be examined using the optometry unit 110, and then inspects the other eye with respect to the base 100 by the drive mechanism. The optometry unit 110 is moved. During this time, based on the image of the eye to be examined obtained by the observation unit 130 at the time of switching, it functions as a control means for performing alignment for examining the other eye to be examined by the drive mechanism.

[flowchart]
In the ophthalmologic apparatus having the above-described configuration, the operation when performing automatic driving will be described based on the flowchart of FIG. 8 and FIG.

  The examiner loads the subject's chin on the chin rest 112 and fixes the right eye E (R) by applying the forehead to the forehead receiving portion of the face receiving frame 113. Next, a full automatic mode is selected with a switch (not shown) on the LCD monitor 109, and the joystick 101 is tilted as necessary to bring the right eye to be examined within the observation range of the LCD monitor 109. The pupil center of E (R) is entered. By pressing the measurement start button 121 from this state, automatic measurement is started.

  When the measurement start button is pressed, first, rough alignment, which is rough alignment for measuring eye refractive power, is started with respect to the right eye E (R) (S100). After the rough alignment is completed (S101), fine alignment, which is more precise alignment, is started (S102). After the fine alignment is completed (S103), the eye refractive power of the right eye E (R) is measured a predetermined number of times (S104). After the measurement of the eye refractive power of the right eye E (R) is completed (S105), the optometry unit 110 is set to X, Y, Z in order to switch left and right from the right eye E (R) to the left eye E (L). Move the required amount in the direction.

  This switching operation is instructed by operating the necessary amount of the joystick 110. The joystick 110 that executes the switching of the left and right examination objects of the eye to be examined in this examination corresponds to the switching means in the present invention. During the switching operation, the positional shift amount of the left eye E (L) is calculated from the pupil position information of the left eye E (L) of the subject from the observation unit 130 at the time of switching, and the left eye E (L) is calculated. On the other hand, rough alignment is performed (S106). As a result, it is not necessary to perform rough alignment after switching, and the optometry time can be shortened.

  After the switching, fine alignment of the left eye E (L) of the subject is started (S107). After the fine alignment is completed (S108), the eye refractive power of the subject's left eye E (L) is measured a predetermined number of times (S109). After the eye refractive power measurement of the left eye E (L) is completed a predetermined number of times (S110), the optometry unit 110 is moved in the X, Y, and Z directions to switch the optometry from the eye refractive power measurement to the intraocular pressure measurement. Move only the required amount. This switching operation is instructed by operating the necessary amount of the joystick 110. The joystick 110 that performs switching of the examinations in a plurality of examinations of the eye to be examined corresponds to the switching means in the present invention.

  During the switching operation, the positional shift amount of the left eye E (L) is calculated from the pupil position information of the left eye E (L) of the subject from the observation unit 130 at the time of switching, and the left eye E (L) is calculated. Rough alignment is performed on the surface (S111). As a result, it is not necessary to perform rough alignment after switching, and the optometry time can be shortened.

  After the switching, fine alignment of the subject's left eye E (L) is started (S112). After the fine alignment is completed (S113), the intraocular pressure of the left eye E (L) is measured a predetermined number of times (S114). After completion of intraocular pressure measurement of the left eye E (L) (S115), the optometry unit 110 is moved in the X, Y, and Z directions in order to switch left and right from the left eye E (L) to the right eye E (R). Move as much as you need.

  During the switching operation, the positional shift amount of the right eye E (R) is calculated from the pupil position information of the right eye E (R) of the subject from the observation unit 130 at the time of switching, and the right eye E (R) is calculated. Rough alignment is performed on the surface (S116). As a result, it is not necessary to perform rough alignment after switching, and the optometry time can be shortened.

  After switching, fine alignment of the subject's right eye E (R) is started (S117). After the fine alignment is completed (S118), the intraocular pressure of the right eye E (R) is measured a predetermined number of times (S119). When the intraocular pressure measurement for the left and right eyes is completed a predetermined number of times (S120), the examination is completed (S121).

  In the embodiment of the present invention, the combined functions are limited to the eye refractive power function and the intraocular pressure function for the sake of simplification, but a plurality of other optometry functions such as a corneal curvature radius measurement function and a corneal thickness measurement function are provided. It can also be applied to the added ophthalmic apparatus. Further, the present invention is not limited to the measurement function, and can be applied to all ophthalmologic apparatuses that inspect an eye to be examined, such as a fundus camera and OCT.

  As described above, in the present invention, the operation of the joystick 110 serving as the switching means is used to switch between examinations between a plurality of examinations with different eyes to be examined, and to switch between left and right examination objects of the eye to be examined in the examinations. Any switching is performed. Further, the module area functioning as the calculation means in the system control unit 401 allows the position of the optometry unit to be preliminarily assumed based on the measurement center and the position of the eye to be examined in the measurement unit, and the actual stop position. Is obtained based on the image obtained by the observation unit. Further, the system control unit 401 determines the stop position of the optometry unit 110 by reflecting the obtained positional deviation and ends rough alignment. Note that the calculating means described here preferably calculates the size of the positional deviation by comparing the image of the eye to be examined obtained before switching and the image obtained by the observation unit of the eye to be examined.

  Further, in this embodiment, regarding the fixation disparity during switching, only the shift in the X and Y directions is described, and the Z direction in which the occurrence of the shift is minute is omitted. However, it is of course possible to monitor the amount of deviation in the Z direction using, for example, a bright spot image on the eye to be examined by external illumination, and perform rough alignment during switching in the Z direction as well as X and Y.

The order of optometry is not limited to eye refractive power measurement → intraocular pressure measurement, right eye to be examined → left eye to be examined. Applicable in any order.
The operation mode is not limited to fully automatic operation. Applicable to all modes such as manual operation and semi-automatic operation.

[Other Examples]
The present invention can also be realized by executing the following processing. That is, software (program) that realizes the functions of the above-described embodiments is supplied to a system or apparatus via a network or various storage media, and a computer (or CPU, MPU, or the like) of the system or apparatus reads the program. It is a process to be executed.

101 Joystick (operation member)
103 X-axis drive motor 104 Y-axis drive motor 108 Z-axis drive motor 109 LCD monitor (display member)
110 Optometry unit 130 Observation unit 131 at the time of switching Image sensor 201 for observation at the time of switching 201 Light source for measuring eye refractive power 210 Image sensor for measuring eye refractive power 220 Image sensor for observing eye 308 Imaging device for observing eye 317 Light source for measuring intraocular pressure E Eye to be examined Ep Pupil of eye to be examined

Claims (13)

The base,
An optometry unit movable in a plurality of directions with respect to the base;
A first optometry unit included in the optometry unit and having an optical system for inspecting a first eye characteristic of the eye to be examined;
A second optometry unit included in the optometry unit and having an optical system for inspecting a second eye characteristic of the eye to be examined;
A drive mechanism capable of driving the optometry unit in a plurality of directions with respect to the base;
Apart from the optometry unit, an observation unit capable of observing the eye to be examined;
While the eye is examined using the first optometry unit, the optometry unit is moved with respect to the base by the drive mechanism in order to perform the second examination by the second optometry unit. An ophthalmologic apparatus comprising: a control unit configured to perform alignment for the second optometry unit by the driving mechanism based on the image of the eye to be examined obtained by the observation unit.   The ophthalmic apparatus according to claim 1, wherein the observation unit is disposed on the base.   The first optometry unit is an optometry unit for examining eye refractive power and the shape of the cornea, and the second optometry unit is an optometry unit for measuring intraocular pressure, The ophthalmic apparatus according to claim 1. The base,
An optometry unit movable in a plurality of directions with respect to the base;
A drive mechanism capable of driving the optometry unit in a plurality of directions with respect to the base;
Apart from the optometry unit, an observation unit capable of observing the eye to be examined;
After inspecting one eye to be examined using the optometry unit, the observation unit while moving the optometry unit with respect to the base by the drive mechanism in order to examine the other eye to be examined An ophthalmologic apparatus comprising: control means for performing alignment for inspecting the other eye to be examined by the drive mechanism based on the obtained image of the eye to be examined. A switching means for switching at least one of the switching of the examination between a plurality of examinations of different examination eyes and the left and right examination targets of the examination eye in the examination;
A drive mechanism for driving the optometry unit for alignment between the optometry unit performing the test and the test object;
An observation unit for observing the examination object during driving of the optometry unit;
Based on the image obtained by the observation unit, the positional deviation between the position when the optometry unit is preliminarily assumed based on the measurement center and the position of the eye to be examined and the position when the optometry unit is actually stopped is determined. Calculating means for obtaining,
The ophthalmologic apparatus characterized in that the drive mechanism reflects the displacement and stops the optometry unit.   The ophthalmologic apparatus according to claim 5, wherein the observation unit is fixed to the ophthalmologic apparatus independently of the optometry unit and the driving mechanism.   The ophthalmologic apparatus according to claim 5 or 6, wherein the observation unit is capable of simultaneously observing the left and right eyes of the eye to be examined.   The calculating means calculates the size of the positional deviation by comparing the image of the eye to be examined obtained before the switching and the image obtained by the observation unit of the eye to be examined. The ophthalmologic apparatus according to any one of claims 5 to 7. Instructing at least one of switching of the examination between a plurality of examinations of different examination eyes, and switching of the left and right examination subjects of the examination eye in the examination,
Driving the optometry unit for aligning the optometry unit that performs the test with the test object in accordance with the instruction;
An ophthalmic examination method for performing the examination after switching after driving the optometry unit,
Observation of the eye to be inspected while the optometry unit is being driven, the position when the optometry unit is stopped and the position when the optometry unit is assumed to be assumed in advance with respect to the measurement center and the position of the eye to be examined Find the position deviation from
An ophthalmic examination method characterized by determining a stop position of the optometry unit by reflecting the displacement.   The observation of the eye to be examined while the optometry unit is being driven is performed using an observing unit that is fixed to the ophthalmologic apparatus independently of the optometry unit and the driving mechanism that drives the optometry unit. The ophthalmic examination method according to claim 9.   The ophthalmic examination method according to claim 9 or 10, wherein the observation unit that observes the eye to be examined while the optometry unit is being driven can simultaneously observe the left and right eyes of the eye to be examined.   The calculation of the positional deviation is performed by comparing the image of the eye to be examined obtained before the switching and the image of the eye to be examined obtained during driving of the optometry unit. Item 12. The ophthalmic examination method according to any one of Items 9 to 11.   A program for causing a computer to execute each step of the ophthalmic examination method according to any one of claims 9 to 12.

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