JP2012010952A - Hand-held ophthalmologic device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a hand-held ophthalmologic device high in operability and capable of making stable measurement/examination.SOLUTION: The hand-held ophthalmologic device includes a device body having an optometric optical system for projecting optometric light flux to an eye to be examined and receiving its reflected light to make the examination or measurement of the eye to be examined; detecting means disposed at the device body to detect a shake applied to the device body; deviation correcting optical means disposed as a part of the optometric optical system to correct the deviation of the optometric light flux caused by the shake applied to the device body; and driving means for driving the deviation correcting optical means based on output from the shake detecting means.

Description

  The present invention relates to a hand-held ophthalmic apparatus that performs eye examination and measurement.

  As an ophthalmologic apparatus for measuring and inspecting an eye, for example, an autorefractometer and a fundus camera are known. Such devices include a stationary device placed in an examination room and a handy device that can be carried (see Patent Document 1).

  In the case of a stationary apparatus, the entire apparatus is three-dimensionally moved by an operation member such as a joystick. And since such an apparatus is large and stable, it is relatively easy to operate with respect to alignment. However, it is difficult to move the apparatus.

JP-A-11-19039

  On the other hand, in the case of a handy type device, the examiner grips the entire device and moves the entire device in three dimensions. In addition, the apparatus may move relative to the eye due to the shake of the examiner. In view of the above, the present situation is that the handy type ophthalmic apparatus is difficult to align and is likely to cause measurement / inspection errors.

  In view of the above problems, an object of the present invention is to provide a hand-held ophthalmologic apparatus that has high operability and can perform stable measurement / inspection.

  In order to solve the above problems, the present invention is characterized by having the following configuration.

(1)
An apparatus main body having an optometry optical system that projects an optometry light beam on the eye to be examined and receives reflected light to inspect or measure the eye to be examined;
A shake detection means disposed on the apparatus body for detecting a shake applied to the apparatus body;
A blur correction optical means for correcting a blur of the optometry light beam that is arranged as a part of the optometry optical system and is shaken on the apparatus main body;
Drive means for driving the shake correction optical means based on the output from the shake detection means;
Is provided.
(2) In the hand-held ophthalmic device according to (1),
The blur detection means includes shift blur detection means for detecting shift blur applied to the apparatus main body.
(3) In the hand-held ophthalmic device of (2),
The blur correction optical means is arranged in a common optical path of the light projecting system and the light receiving system of the optometry optical system or in each of the light projecting system and the light receiving system of the optometry optical system.
(4) In the hand-held ophthalmic device of (3),
The apparatus main body further includes an imaging optical system that captures a front image of the eye to be inspected with an imaging element,
The blur correction optical means is arranged in a common optical path of the optometry optical system and the imaging optical system.
(5) In the hand-held ophthalmic device according to (4),
The blur correction optical means is a light deflection member that deflects the optometry light beam.
(6) In the hand-held ophthalmic device according to (5),
The light deflecting member is a light reflecting member that reflects the optometry light beam toward the subject's eye.
(7) In the hand-held ophthalmic device according to (6),
The optometry optical system is an eye refracting power measurement optical system that projects a measurement index onto the fundus of the subject's eye, receives the fundus reflection light flux, and measures eye refracting power.
(8) In the hand-held ophthalmic device according to (7),
The driving means drives the blur correction optical means so that a measurement region by the eye refractive power measurement optical system is positioned on the pupil of the eye to be examined.

  According to the present invention, operability is high and stable measurement / inspection can be performed.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings. FIG. 1 is an external side view showing an example of a hand-held ophthalmologic apparatus according to the present embodiment. Hereinafter, an eye refractive power measuring apparatus (autorefractometer) will be described as an example. In the following description, the positional relationship between the eye to be examined and the apparatus will be described with the front-rear direction as the Z direction, the left-right direction as the X direction, and the vertical direction as the Y direction.

  The apparatus main body 100 includes an optical unit 1 that includes an optometry optical system 10 that projects an optometry light beam onto the eye E and receives the reflected light, and a shake that detects movement (for example, camera shake of the examiner) applied to the apparatus main body 100. A detection unit 60 and a shake correction unit 70 for correcting the shake of the optometry light beam due to the shake applied to the apparatus main body 100 are provided. The inspection window 102 is disposed on the eye E side of the main body 100. The operation unit 84 and the monitor 85 are disposed on the examiner side of the main body 100. Furthermore, the apparatus main body 100 houses an electrical system for control and arithmetic processing. The examiner faces the subject and holds the main body 100. Then, the main body 100 is aligned with the eye E while looking at the monitor 85.

  The shake correction unit 70 includes a reflection mirror 72 as a shake correction optical system, and a drive unit (for example, a boil coil motor mechanism) 74 that rotates the reflection mirror 72 in the XY directions. The reflection mirror 72 is disposed in any one of the optical paths of the optometry optical system 10 and is used as a part of the optometry optical system 10. A configuration in which a plurality of reflection correcting mirrors are provided (for example, a galvano motor mechanism is used) may be used. In this case, one is rotated in the X direction and the other is rotated in the Y direction. .

  In FIG. 1, the reflection mirror 72 is disposed at a position facing the eye E, and the optometry optical system 10 is disposed below the reflection mirror 72. The optical axis L1 of the optometry optical system 10 is bent in the direction of the eye E by the reflection mirror 72. The reflection mirror 72 reflects the outgoing light from the optometry optical system 10 and guides it to the eye E, and reflects the reflected light from the eye E and guides it to the optometry optical system 10.

  The reflection mirror 72 is rotated around an intersection K between the optical axis L1 and the reflection mirror 72. The reference position of the reflection mirror 72 is a position where the optical axis L1 is parallel to the Z direction. When the reflection mirror 72 is rotated, the optical axis L1 is turned around a predetermined point O on the optical axis L1 (see FIG. 5). The predetermined point O coincides with the pupil center Pc by alignment.

  The detection unit 60 has at least one angular velocity sensor or acceleration sensor, and detects the shake state of the apparatus main body 100. The detection unit 60 is connected to the drive unit 74, and the drive unit 74 is connected to the reflection mirror 72. In such a configuration, the shake detection unit 60 detects the shake amount, and the drive unit 74 drives the reflection mirror 72 based on the output of the shake detection unit 60.

  In FIG. 1, the detection unit 60 has an acceleration sensor 62. The acceleration sensor 62 outputs an acceleration signal corresponding to the parallel shake (shift shake) of the apparatus main body 100 in the XY directions. In addition to the XY biaxial sensor, a sensor that detects parallel shake in the Z direction may be provided. Further, only a single-axis sensor may be used. The acceleration sensor 62 may be a mechanical, optical, or semiconductor (capacitance type, piezoresistive type, gas temperature distribution type) acceleration sensor. The reason why the acceleration sensor 62 is used is that the distance between the apparatus main body 100 and the eye E is relatively short in eye inspection / measurement, and parallel blurring by the examiner is likely to occur. In addition to the acceleration sensor 62, an angular velocity sensor may be provided. In this case, an angular velocity signal corresponding to the rotational shake of the apparatus main body 100 is output.

  FIG. 2 is an optical layout view of the optical system housed in the main body 100 as viewed from the front. The optical unit 1 includes an optometry optical system 10, a projection optical system 30 for projecting a fixation target onto the eye E, and an observation optical system 50 for observing the eye E.

  In FIG. 2, an optometry optical system 10 is an optical system for objectively measuring eye refractive power. The optometry optical system 10 projects a measurement index on the fundus oculi Ef and receives the fundus reflection light flux. Then, the refractive power of the eye E is measured based on the received light signal.

  More specifically, the optometry optical system 10 takes out a light projection optical system 10 that projects a spot index on the fundus oculi Ef via the pupil center Pc, and takes out the fundus reflection light from the periphery of the pupil in a ring shape, And a light receiving optical system 20 for picking up a ring-shaped reflection image.

  The light projecting optical system 10 a includes a light source 11, a relay lens 12, a hall mirror 13, an objective lens 14, and a reflection mirror 72 arranged on the optical axis L <b> 1. The light source 11 is disposed at a substantially conjugate position with the fundus oculi Ef, and the opening of the hall mirror 13 is disposed at a substantially conjugate position with the pupil of the eye E.

  The measurement light emitted from the light source 11 is reflected by the reflection mirror 72 via the light source 11, the relay lens 12, the hall mirror 13, the dichroic mirror 35, the dichroic mirror 53, and the objective lens 14. Then, the measurement light reflected by the reflection mirror 72 passes through the pupil center Pc, and a spot-like light beam is projected onto the fundus oculi Ef.

  The light receiving optical system 10 b includes a reflection mirror 72, an objective lens 14, a hall mirror 13, a collimator lens 22, a ring lens 24, and an image sensor (for example, a two-dimensional image sensor such as a CCD or a CMOS) 26. The image sensor 26 is disposed at a position substantially conjugate with the fundus oculi Ef via the lens 14, the lens 22, and the ring lens 24. The ring lens 20 includes a lens portion in which a cylindrical lens is formed in a ring shape, and a light shielding portion having a ring opening having the same size as the lens portion, and is disposed at a position substantially conjugate with the pupil of the eye E. . An output signal from the image sensor 22 is connected to the control unit 80.

  Then, the fundus reflected light beam by the light projecting optical system 10 a is reflected again by the reflecting mirror 72, reflected by the reflecting surfaces of the objective lens 14, the dichroic mirror 53, the dichroic mirror 35, and the hall mirror 13, and substantially parallel by the collimator lens 22. A light beam (in the case of a normal eye) is extracted as a ring-shaped light beam by the ring lens 24 and received by the image sensor 24 as a ring image.

  In addition to the above configuration, a ring index is projected onto the fundus oculi Ef from the periphery of the pupil, a reflected light is extracted from the center of the pupil, and a ring image is received on the image sensor, and a phase difference method is projected on the fundus Various methods such as can be adopted.

  Between the objective lens 14 and the hall mirror 13, a dichroic mirror 35 for visible reflection and infrared transmission is disposed as a beam splitter, and light from the light source 31 is guided toward the eye E. A dichroic mirror 53 is disposed as a beam splitter between the dichroic mirror 35 and the objective lens 14, and light from the anterior eye part is guided to the observation optical system 50. The mirror 53 has a wavelength characteristic that transmits the measurement light beam and reflects the observation light beam. By these beam splitters, the measurement optical axis, the fixation optical axis, and the observation optical axis are arranged on the same optical axis (L1).

  The projection optical system 30 includes a light source 31 that emits visible light, a fixation target 32 on which a landscape / animal is drawn, a projection lens 33, a total reflection mirror 34, a dichroic mirror 35, an objective lens 14, and a reflection mirror 72. In addition to the above configuration, a point light source such as an LED or a display such as a liquid crystal panel is used as a fixation target. A plurality of fixation targets may be arranged two-dimensionally.

  The fixation target 32 illuminated by the light source 31 is projected onto the fundus oculi Ef via the light projection lens 33, the total reflection mirror 34, the dichroic mirror 35, the dichroic mirror 53, the objective lens 14, and the reflection mirror 72. Thereby, the eye E is fixed. Further, the light source 31 and the fixation target 32 are moved in the optical axis direction, and clouding is applied to the eye E.

  Further, outside the inspection window 102, a first projection optical system 45 that projects a ring-shaped finite distance index onto the cornea Ec is disposed concentrically with the optical axis L1. Further, the second projection optical system 46 that projects the infinity index onto the cornea Ec is disposed symmetrically with respect to the optical axis L1 (up and down for convenience in the drawing). The first projection optical system 45 illuminates the anterior segment with infrared light. It can also be used as a corneal shape measurement index (kerato index).

  The observation optical system 50 includes a reflection mirror 72, an objective lens 14, a dichroic mirror 53, an imaging lens 51, and a two-dimensional imaging element 52. An output signal from the image sensor 52 is connected to the control unit 80 and output to the monitor 85. The observation optical system 50 is used as a detection optical system that detects the front image of the eye E and detects the alignment state of the apparatus main body 100 with respect to the eye E.

  The anterior segment image of the eye E illuminated by the first projection optical system 45 is received by the imaging surface of the imaging element 52 via the reflection mirror 72, the objective lens 14, the dichroic mirror 53, and the imaging lens 51. Similarly, an alignment index image by the first projection optical system 45 and the second projection optical system 46 is detected by the image sensor 52.

  FIG. 3 is a block diagram showing the electricity / control system housed in the main body 100. The control unit 80 performs arithmetic processing such as control of the entire apparatus and calculation of an eye refraction value. The control unit 80 is connected to the light source 11, the image sensor 26, the light source 31, the image sensor 52, an operation unit 84 used for various settings, a monitor 85, a shake detection unit 60, a shake correction unit 70, a memory 81, and the like. Yes. For the operation of the detection unit 60 and the correction unit 70 by the control unit 80, a dedicated drive circuit (for example, LSI) may be used for speeding up. Of course, it may be operated by software.

  Note that the control unit 80 controls the display of the monitor 85 to superimpose and display an anterior segment image, a measurement result, and the like on the screen. Further, the control unit 80 detects misalignment based on the image signal from the image sensor 52.

  FIG. 4 is a ring image captured by the image sensor 26 during measurement. The output signal from the image sensor 26 is stored in the memory 81 as image data (measurement image). Thereafter, the control unit 80 detects the image position in each meridian direction based on the image stored in the memory 81, and then performs elliptic approximation using the least square method or the like. And the control part 80 calculates | requires the refraction error of each meridian direction from the approximate ellipse shape, and based on this, an eye refraction value, S (spherical power), C (columnar surface frequency), and A (astigmatic axis angle) are obtained. Measure and display the result on the monitor 85.

  The operation of the apparatus having the above configuration will be described. The examiner holds the apparatus main body 100 and gives an instruction to fixate the fixation target 32, and then places the inspection window 102 in front of the eye E. As a result, the anterior segment is imaged by the imaging element 52 and projected onto the monitor 85 by the anterior segment image F, the ring image (Meyer ring image) R by the first projection optical system 45, and the second projection optical system 46. The infinity index image M is displayed (see FIG. 3).

  Then, the control unit 80 detects the alignment state with respect to the eye to be examined based on the imaging signal from the imaging element 52. In this case, the control unit 80 calculates the misalignment in the XY directions by calculating the center position (substantially the cornea center) of the ring index R. Further, the control unit 80 utilizes the characteristic that when the apparatus main body 100 is displaced in the Z direction, the interval between the indexes M hardly changes, whereas the image interval of the ring index R changes. (See Japanese Patent Application Laid-Open No. 6-46999 for details). The controller 80 increases or decreases the number of indicators G based on the alignment detection result in the Z direction.

  Here, the examiner moves the apparatus main body 100 in the XY directions so that the ring image R and the reticle mark LT are concentric. Further, the apparatus main body 100 is moved in the Z direction while referring to the indicator G that changes based on the alignment detection result in the Z direction (or so that the ring image R becomes the thinnest).

  Thereafter, when the auto-shot is activated, the control unit 80 generates a trigger signal for starting measurement when the alignment state in the XYZ directions satisfies an allowable range. On the other hand, when the auto shot is OFF, measurement is started when a trigger switch provided on the operation unit 84 is pressed.

  When the trigger signal is output, the control unit 80 turns on the light source 11 and projects a measurement index on the fundus oculi Ef. Then, the control unit 80 receives the reflected light by the image sensor 26 and detects an index image.

  At this time, preliminary measurement is first performed, and based on the result, the light source 31 and the fixation target plate 32 are moved in the optical axis direction, and a cloud is applied to the eye E. Thereafter, the main measurement is performed on the eye E. In this measurement, ring image addition / accumulation processing or measurement is performed a plurality of times, so that images of a plurality of frames are acquired and stored in the memory 81.

  During the measurement, the control unit 80 supplies power to the sensor 62 and generates a position displacement signal based on the acceleration signal output from the sensor 62. Then, the control unit 80 receives the generated position displacement signal as an input and outputs a shake correction signal for rotating the reflection mirror 72 in a direction in which the shift shake of the apparatus main body 100 is canceled.

  FIG. 5 is a specific example when correcting camera shake at the time of measurement. FIG. 5A shows a state before camera shake occurs, and FIG. 5B shows a state immediately after shift deviation occurs due to camera shake. FIG. 5C shows a state after the shift deviation is corrected. The control unit 80 drives the shake correction unit 70 so that the measurement region by the eye refractive power measurement optical system is positioned on the pupil.

  In order to correct camera shake, the optical axis L1 in the direction opposite to the movement of the apparatus main body 100 is canceled so as to cancel out the shift of the optical axis L1 with respect to the center of the eye E (for example, the pupil center Pu or the corneal center). Is moved. In addition, even if it is not complete, it is sufficient that the deviation of the optical axis L1 is suppressed.

  For example, when the apparatus main body 100 is shifted downward by ΔY with respect to the line-of-sight direction of the eye E due to camera shake of the examiner, a downward displacement amount ΔY is generated as a position displacement signal. The control unit 80 drives the drive unit 74 to rotate the reflection mirror 72 upward by Δθ so that the optical axis L1 is turned around the pupil center Pc as a turning point.

  The measurement light beam from the light projecting optical system 10a is corrected (deflected) by the movement of the reflection mirror 72 and projected onto the fundus oculi Ef through the pupil center Pu. Then, the reflected light beam from the fundus is reflected by the reflection mirror 72, is coaxial with the optical axis of the objective lens 14, and travels toward the image sensor 26. The measurement area by the optometry optical system 10 is tracked with respect to the pupil of the eye E.

  Similarly, since the fixation light flux of the projection optical system 30 is corrected (deflected) by the movement of the reflection mirror 72, the eye E is guided, and the visual axis of the eye E and the optical axis L1 become coaxial. That is, the fixation direction of the eye E is tracked with respect to the optical axis L1. Depending on the reaction speed of the eye E, there may be cases where the fixation direction remains the front direction. When the projection optical system 30 is arranged independently of the reflection mirror 72, the eye E is fixed in the front direction.

  The reflected light beam from the anterior segment is reflected by the reflecting mirror 72, is coaxial with the optical axis of the objective lens 14, and travels toward the image sensor 52. The observation area by the observation optical system 50 is tracked with respect to the anterior segment of the eye E.

  As a result, even when the apparatus main body 100 moves due to the shaking of the examiner, measurement of eye refractive power, fixation fixation guidance, and anterior ocular segment observation are possible. In this case, measurement light is projected and received continuously (for example, a measurement image of a plurality of frames is obtained) to measure the refractive power, which is particularly advantageous. In the above description, only the Y direction has been described as an example. However, by performing the same control in the X direction, the positional deviation in the XY direction due to camera shake is corrected.

  As described above, by detecting the shift of the optical axis L1 with respect to the eye E and driving the correction optical system, it is possible to perform stable measurement / inspection even for a hand-held ophthalmic apparatus that is difficult to align.

  As shown in FIG. 2, the blur correction optical system (72) is arranged in the common light path of the light projecting system and the light receiving system of the optometry optical system 10, so that the incident position and the exit position of the light flux with respect to the eye are properly adjusted. Corrected and measured (inspected) with high accuracy. Note that a shake correction optical system may be disposed in each of the light projecting system and the light receiving system.

  Further, as shown in FIG. 2, since the shake correction optical system is arranged in the common optical path of the optometry optical system 10 and the observation optical system 50, the shake of the observation image is also corrected, so that stable observation and measurement ( Inspection) is possible.

  Further, in the above, a light reflecting member (for example, a reflecting mirror or a reflecting prism) is used as a correcting optical member for deflecting the optometry light beam for correcting the deviation. Thereby, since the incident light on the correction optical member is directed to the eye E, the incidence of disturbance light on the optometry light-receiving element is preferably avoided when the optical member is moved.

  In this case, a light beam deflecting member (for example, a prism) is provided at a position deviating from the pupil conjugate position, and the disturbance light is more suitably removed by rotating the member eccentrically about the optical axis L1.

  Of course, even with other correction optical members, certain effects can be obtained. In this case, it is preferable that the optical member be moved so that the conjugate relationship between the pupil of the eye E and the ring lens 24 in the XY directions is maintained when the positions of the apparatus main body 100 and the eye E are shifted. For example, the objective lens 14 disposed in the common optical path of the light projecting optical path and the light receiving optical path may be moved perpendicular to the optical axis. Of course, an optical member dedicated to optical axis misalignment (for example, a concave lens) may be disposed. Moreover, a plurality of optical members may be used.

  Further, the ring lens 24 and the image sensor 26 may be moved in a direction perpendicular to the optical axis of the lens 22 (the light source 11 may be moved in conjunction). Note that the image sensor 26 may be used as a shake detection system. For example, based on the image signal from the image sensor 26, the correction optical system is moved so that the center of the ring image on the image sensor 26 coincides with the optical axis.

  In the above description, the sensor (detection unit 60) that detects the movement of the apparatus main body 100 is used. However, an image sensor that images the eye E may be used as the shake detection sensor. For example, the control unit 80 detects a shake from the imaging result of the imaging device 52, and the center of the cornea (or the pupil center may be within an allowable range from the alignment reference position (for example, the intersection of the imaging surface and the optical axis L1). The correction optical system is feedback-driven so that Note that according to this method, even when the eye E moves relative to the apparatus main body 100 within the driving range of the correction optical system, the positional deviation is corrected.

  Further, in the above description, the camera shake detection and correction operation may be started when an alignment deviation satisfies a certain allowable range (for example, wider than the alignment completion range). In addition, the camera shake correction operation may be started using an output signal from the operation unit 84 as a trigger.

  When detecting an alignment deviation from the output of the image sensor 52, the deviation amount detected by the detection unit 60 may be offset (corrected) with respect to the actual deviation amount. Further, at the time of camera shake correction, the alignment detection and result output may be stopped.

  In the above description, the autorefractometer has been described as an example. However, the present invention can also be applied to other ophthalmologic apparatuses. For example, the present invention can be applied to a handy type fundus photographing apparatus (for example, a fundus camera or an ophthalmic OCT). In this case, a shift between the imaging optical axis and the eye E due to camera shake is detected, and the correction optical system is driven based on the detection signal.

  For example, in the case of an apparatus that images the fundus, the control unit detects blur of the fundus image captured by the fundus imaging (for example, alignment) imaging element provided in the fundus observation optical system, and the blur is corrected. As described above, the correction optical system may be feedback-driven. Of course, an acceleration sensor or the like may be provided.

  Note that the present invention can be applied to a case where the apparatus is placed in an unstable place even if it is a stationary ophthalmic apparatus instead of a hand-held ophthalmic apparatus.

  In the above description, in a hand-held ophthalmic apparatus that projects a measurement light beam onto the fundus and receives the reflected light beam to measure eye characteristics (for example, eye refractive power, axial length), Although the sensor for detecting the added shake is used, the present invention is not limited to this.

  For example, a light beam deflecting member (for example, a prism, a mirror, etc.) is provided in the optical path of the measurement optical system, and the light beam deflecting member is driven to change the measurement light beam passing region on the anterior eye portion as needed for measurement. May be. The light beam deflecting member is disposed, for example, at a position deviating from the pupil conjugate position of the measurement optical system. More specifically, the prism is eccentrically rotated about the optical axis L1, and the passing region is eccentrically rotated. Further, the mirror is reciprocated up and down, and the passing area is moved up and down.

  In this way, the measurement light beam shift area cancels out the shift of the measurement light beam due to camera shake by the high-speed movement of the measurement light beam passage region with respect to the anterior segment. Therefore, the measurement is easily performed by receiving the measurement light beam at the time of cancellation and performing the measurement.

It is an external appearance side view which shows an example of the hand-held ophthalmic apparatus which concerns on this embodiment. It is the optical arrangement figure which looked at the optical system stored in the main part from the front. It is a block diagram which shows the electricity and control system accommodated in the main body. It is a ring image imaged by an image sensor in the case of a measurement. It is a specific example at the time of correcting camera shake at the time of measurement.

DESCRIPTION OF SYMBOLS 10 Optometry optical system 50 Observation optical system 52 Image pick-up element 60 Camera shake detection unit 70 Camera shake correction unit 72 Reflection mirror 74 Drive part 100 Apparatus main body

Claims (8)

An apparatus main body having an optometry optical system that projects an optometry light beam on the eye to be examined and receives reflected light to inspect or measure the eye to be examined;
A shake detection means disposed on the apparatus body for detecting a shake applied to the apparatus body;
A blur correction optical means for correcting a blur of the optometry light beam that is arranged as a part of the optometry optical system and is shaken on the apparatus main body;
Drive means for driving the shake correction optical means based on the output from the shake detection means;
A hand-held ophthalmic device. The handheld ophthalmic device according to claim 1,
The hand-held ophthalmologic apparatus, wherein the shake detecting means includes shift shake detecting means for detecting shift shake applied to the apparatus main body. The handheld ophthalmic device according to claim 2,
The hand movement type ophthalmologic apparatus is characterized in that the blur correction optical means is disposed in a common optical path of the light projecting system and the light receiving system of the optometry optical system or in each of the light projecting system and the light receiving system of the optometry optical system. . The handheld ophthalmic device according to claim 3,
The apparatus main body further includes an imaging optical system that captures a front image of the eye to be inspected with an imaging element,
The hand-held ophthalmologic apparatus, wherein the blur correction optical means is disposed in a common optical path of the optometry optical system and the imaging optical system. The hand-held ophthalmic device according to claim 4,
The hand-held ophthalmologic apparatus, wherein the blur correction optical means is a light deflection member that deflects the optometry light beam. The handheld ophthalmic device according to claim 5,
The hand-held ophthalmic apparatus, wherein the light deflecting member is a light reflecting member that reflects the optometry light beam toward the subject's eye. The hand-held ophthalmic device according to claim 6,
The optometry optical system is an ophthalmic power measurement optical system that projects a measurement index onto the fundus of the subject's eye and receives the fundus reflection light flux to measure the eye refractive power. The handheld ophthalmic device according to claim 7,
The hand-held ophthalmic apparatus characterized in that the driving means drives the blur correction optical means so that a measurement region by the eye refractive power measurement optical system is positioned on a pupil of an eye to be examined.

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