JP2017221794A - Ophthalmologic device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ophthalmologic device which can set a position of one eye to be examined on a face which is moved, as a reference position, even when a subject moves his/her face after measurement.SOLUTION: An ophthalmologic device 10 comprises: a measurement part (40) for measuring eyes to be examined E of a subject; a drive part 12 for moving the measurement part (40) to the eyes to be examined E; and a control part 33 for controlling the measurement part (40) and the drive part 12. The control part 33 measures one eye to be examined E by the measurement part (40) after performing alignment of the measurement part (40) to one eye to be examined E, then performs alignment of the measurement part (40) to the one eye to be examined E after measuring the one eye to be examined E, and stores a position of the measurement part (40) in a state in which the alignment is completed.SELECTED DRAWING: Figure 9

Description

  The present invention relates to a composite ophthalmologic apparatus provided with a first measurement unit set at a first set working distance and a second measurement unit set at a second set working distance.

  In the ophthalmologic apparatus, the first measuring unit set to the first set working distance and the second measuring unit set to the second set working distance shorter than the first set working distance are provided. An ophthalmologic apparatus has been proposed (see, for example, Patent Document 1). In this ophthalmologic apparatus, an intraocular pressure measuring unit in which the second set working distance is set to a very small value is provided as the second measuring unit, and the first set working distance is a relatively large value as the first measuring unit. The other eye characteristic measuring unit is provided. In the ophthalmologic apparatus, the first measurement unit is automatically moved to a position where measurement can be appropriately performed on both of the examinee's eyes, and each measurement is performed. Each of the measurements is automatically moved to a position where measurement can be appropriately performed. Thereby, in an ophthalmologic apparatus, the measurement of each eye to be examined by the 1st measurement part and the 2nd measurement part can be performed simply and smoothly.

JP 2010-148589 A

  However, in the conventional ophthalmologic apparatus described above, it is necessary to automatically move the first measurement unit and the second measurement unit from the position suitable for one eye to the position suitable for the other eye. The moving distance, that is, the distance between both eyes of the subject's eyes varies depending on the subject. For this reason, it is conceivable to move using the average value of the binocular intervals of a large number of subjects, but it is difficult to appropriately deal with all subjects.

  From this, it is considered that the eye to be examined (its pupil etc.) is detected as the target of movement using the image of the eye to be examined acquired by the observation optical system in each of the first measuring unit and the second measuring unit. It is done. However, since the second set working distance is set to a very small value in the second measurement unit, when moving from a position suitable for one eye to a position suitable for the other eye, It is necessary to move backward so as not to interfere with the person's nose and the like so as to be away from the eye to be examined. For this reason, since the second measuring unit detects the eye to be examined (pupil or the like) in a state of being far away from the second set working distance, the observation optics provided for itself and adapted to the second set working distance. In the system, there is a possibility that a scene in which the eye to be examined (pupil or the like) cannot be detected properly occurs.

  The present invention has been made in view of the above circumstances, and even if the subject moves his / her face after measurement, the position of one of the subject's eyes in the moved face is used as a reference. An object of the present invention is to provide an ophthalmologic apparatus that can perform such operations.

  In order to solve the above-described problem, the ophthalmologic apparatus according to claim 1 includes a measurement unit that measures an eye of a subject, a drive unit that moves the measurement unit with respect to the eye, and the measurement And a control unit that controls the driving unit, the control unit measures the one eye to be examined by the measurement unit after performing alignment of the measurement unit with respect to the one eye to be examined, After the measurement of the eye to be examined, the measurement unit is aligned with respect to one eye to be examined, and the position of the measurement unit in a state in which the alignment is completed is stored.

  The ophthalmologic apparatus according to claim 2 is the ophthalmologic apparatus according to claim 1, wherein the control unit stores the position of the measurement unit in a state where alignment after measurement is completed, and then the other eye to be examined. The measurement unit is moved to the side.

  The ophthalmologic apparatus according to claim 3 is the ophthalmologic apparatus according to claim 2, wherein the control unit aligns and stores the measurement unit with respect to the other eye to be examined after moving the measurement unit. Based on the position of the measurement unit that has been aligned with respect to the eye to be examined and the position of the measurement unit that has been aligned with respect to the other eye to be examined after movement, the binocular interval of the eye to be examined is determined. It is characterized by seeking.

  According to the ophthalmologic apparatus of the present invention, even when the subject moves his / her face after measurement, the position of one of the subject's eyes on the moved face can be used as a reference.

  A first measurement unit set at a first set working distance for measuring the subject's eye, and a second set working distance shorter than the first set working distance for measuring the subject eye. A second measuring unit, a driving unit for moving the first measuring unit and the second measuring unit with respect to the eye to be examined, the first measuring unit, the second measuring unit, and the driving unit. A control unit that controls the left and right when the first measurement unit is moved to measure the left and right eyes of the subject using the first measurement unit. After obtaining the binocular interval of the eye to be examined and measuring one eye to be examined using the second measuring unit, the second measuring unit is moved toward the other eye side by the obtained binocular interval. According to the ophthalmologic apparatus, the second measuring unit set to the second set working distance that is smaller than the first set working distance is provided. It can be properly moved from the compatible position on one of the eye to fit at the other of the eye automatically.

  In addition to the above-described configuration, the control unit obtains the second measuring unit after measuring the one eye to be examined and then aligning the second measuring unit with respect to the one eye to be examined. If the second measurement unit is moved toward the other eye side by the interval between both eyes, the second measurement unit can be automatically moved more appropriately to a position facing the other eye.

  In addition to the above-described configuration, the control unit includes the position of the first measurement unit that has been aligned with respect to one eye to be examined, and the first measurement unit that has been aligned with respect to the other eye to be examined. If the distance between the eyes is determined based on the position of the eye, the distance between the eyes can be determined more appropriately.

  In addition to the configuration described above, the control unit measures the position of the first eye using the first measurement unit, and then performs alignment on the one eye to be examined. Then, if the distance between the eyes is determined based on the position of the first measurement unit that has been aligned with respect to the other eye, the subject has moved his face. Also, the distance between both eyes can be obtained appropriately.

  In addition to the above-described configuration, if the second measurement unit is an intraocular pressure measurement unit that measures the intraocular pressure by spraying a fluid on the cornea of the eye to be examined and deforming the cornea, Even when the examiner has moved his / her face, the second measurement unit can be automatically moved to a position more appropriately facing the other eye to be examined.

  In addition to the configuration described above, the first measurement unit includes a first observation optical system that acquires an image of the anterior segment of the eye to be examined, and the control unit acquires the first observation optical system. The position of the pupil in the anterior eye part can be acquired based on the image of the anterior eye part, and is acquired based on the image of the anterior eye part after measuring the one eye to be examined using the first measuring part. When the first measurement unit is moved toward the other eye side with the position of the pupil of the other eye to be examined as a target, the interocular interval can be obtained with high accuracy by the first measurement unit, Since the second measurement unit is moved to the other eye side using the binocular interval, the second measurement unit can be automatically and appropriately moved to a position facing the other eye.

  In addition to the configuration described above, the control unit obtains movement amounts of the first measurement unit in the vertical direction, the horizontal direction, and the front-rear direction orthogonal to each other in the ophthalmic apparatus as the binocular interval, When the second measuring unit is moved by the respective movement amounts in the up and down direction, the left and right direction, and the front and back direction obtained as the interval, the second measuring unit is simplified while simplifying control for movement. Can be automatically moved to a position more appropriately facing the other eye.

  In addition to the above-described configuration, when the control unit obtains the binocular interval from the positions of the corneal vertices of the left and right eyes, for example, the second measurement unit can detect the corneal vertex (the position thereof) of the cornea of the eye to be examined. ) And the optical axis are matched to perform measurement, the second measurement unit can be appropriately matched to bring the second measurement unit to a position more appropriately facing the other eye to be examined. It can be moved automatically.

  In addition to the configuration described above, the first measurement unit includes a first observation optical system that acquires an image of the anterior segment of the eye to be examined, and the second measurement unit is configured to detect an anterior segment of the eye to be examined. Assuming that the second observation optical system has an image acquisition and the second observation optical system is set to a higher magnification than the first observation optical system, the second measurement unit uses a binocular interval. It can be made more effective to move to the other eye side.

It is explanatory drawing which shows typically the structure of the ophthalmologic apparatus 10 of the Example which concerns on this invention. 3 is an explanatory diagram for explaining an optical configuration of an intraocular pressure measurement unit 20 of the ophthalmologic apparatus 10. FIG. FIG. 3 is an explanatory diagram viewed from a direction different from FIG. 2 for describing an optical configuration of an intraocular pressure measurement unit 20 of the ophthalmologic apparatus 10. 4 is an explanatory diagram for explaining an optical configuration of an eye characteristic measurement unit 40 of the ophthalmologic apparatus 10. FIG. It is explanatory drawing for demonstrating a mode that the apparatus main-body part 13 is moved and switching a measurement mode, (a) shows the state made into the intraocular pressure measurement mode, (b) shows the state made into the eye characteristic measurement mode Indicates. It is explanatory drawing for demonstrating the predetermined height position HL and the predetermined front position FL using the positional relationship of the apparatus main body part 13 and the forehead holding | maintenance part 16, (a) shows the predetermined height position HL. , (B) shows a predetermined forward position FL. In the eye characteristic measurement unit 40 of the ophthalmologic apparatus 10, it is an explanatory diagram for explaining a switching operation from a position suitable for the left subject eye EL to a position suitable for the right subject eye ER. The main optical axis O10 of the eye characteristic measuring unit 40 is aligned with the subject eye EL, and (b) illustrates the main optical axis O10 of the eye characteristic measuring unit 40 aligned with the right eye ER. . A state in which both eyes E move in the image (its data) acquired by the observation optical system 42 when the apparatus main body 13 (eye characteristic measurement unit 40) is moved from the eye EL side to the eye ER to be examined. It is explanatory drawing for demonstrating, (a) shows the scene where to-be-tested eye EL remove | deviates from an image, (b) shows the scene where the to-be-tested eye ER began to enter into an image after (a). (C) shows the scene after (b) and the pupil Ep of the eye ER to be examined entered the image. It is a flowchart which shows the left-right eye switching operation | movement process (left-right eye switching operation method) performed by the control part 33 in a present Example. FIG. 6 is an explanatory diagram for explaining a switching operation from a position suitable for the right eye ER to a position suitable for the left eye EL in the intraocular pressure measurement unit 20 of the ophthalmic apparatus 10, and FIG. The state in which the optical axis O1 of the intraocular pressure measuring unit 20 is aligned with the eye ER to be examined is shown, (b) shows the state in which the intraocular pressure measuring unit 20 is retracted from the state of (a), and (c) is (b) ) Shows the state in which the tonometry part 20 moves in the X-axis direction and the optical axis O1 of the tonometry part 20 is aligned with the left eye EL, and (d) shows the state from (c). A state in which the intraocular pressure measurement unit 20 is moved to the eye to be examined EL side is shown. It is explanatory drawing which shows a mode that the airflow spray nozzle 21b of the state which shifted out of focus exists in the image (the data) acquired with the anterior ocular segment observation optical system 21. FIG.

  Embodiments of an ophthalmologic apparatus according to the present invention will be described below with reference to the drawings.

  An ophthalmologic apparatus 10 as an embodiment of an ophthalmologic apparatus according to the present invention will be described with reference to FIGS. As shown in FIG. 1, the ophthalmologic apparatus 10 includes an intraocular pressure measurement unit 20 that measures the intraocular pressure of the eye E (see FIG. 2 and the like) and an eye that measures other optical characteristics (eye characteristics) of the eye E. And a characteristic measurement unit 40. As for the eye E, FIGS. 2 and 3 show a fundus (retina) Ef, a cornea (anterior eye portion) Ec, and a corneal apex Ea. The ophthalmologic apparatus 10 is configured by providing a base 11 with an apparatus main body 13 via a drive unit 12. The apparatus main body 13 is provided with an intraocular pressure measurement unit 20 and an eye characteristic measurement unit 40 on the inner side, and with a display unit 14, a chin rest 15 and a forehead support unit 16 on the outer side.

  The display unit 14 is formed of a liquid crystal display, and displays an image such as an anterior segment image of the eye E, a test result, and the like under the control of a control unit 33 (see FIG. 2) described later. In this embodiment, the display unit 14 has a touch panel function, and moves the apparatus main body 13 by an operation for performing measurement using the intraocular pressure measurement unit 20 or the eye characteristic measurement unit 40 or manually. It is possible to perform an operation for this. In addition, the display unit 14 displays a switching icon in each measurement mode to be described later using the function of the touch panel, and enables the switching operation of each measurement mode by touching the switching icon. The operation for performing the measurement may be performed by providing a measurement switch and operating the measurement switch. Further, an operation for moving the apparatus main body 13 may be performed by providing a control lever or a movement operation switch and operating the control lever or the movement operation switch.

  The chin rest 15 and the forehead support 16 fix the face of the subject (patient), that is, the position of the eye E to be measured with respect to the apparatus main body 13, and are fixed to the base 11. ing. The chin receiving portion 15 is a place where the subject places his chin, and the forehead holding portion 16 is a place where the subject places the forehead. In this ophthalmic apparatus 10, the display unit 14, the chin rest 15 and the forehead support 16 are provided on both sides of the apparatus main body 13, and the display unit 14 is inspected during normal use. The chin rest 15 and the forehead support 16 are on the subject side. The display unit 14 is rotatably supported by the apparatus main body unit 13 to change the orientation of the display surface, for example, to direct the display surface toward the subject, or to display the display surface sideways (X-axis). Direction). The apparatus main body 13 moves with respect to the base 11 by the drive unit 12, that is, moves with respect to the eye E (face of the subject) fixed by the jaw holder 15 and the forehead support 16. It is possible to do.

  The drive unit 12 is perpendicular to the vertical direction (Y-axis direction) and the front-rear direction (Z-axis direction (left-right direction when FIG. 1 is viewed from the front)) of the apparatus main body 13 with respect to the base 11. In this embodiment, the upper side in the vertical direction is the positive side in the Y-axis direction, and the subject side in the front-rear direction ( 1 is the positive side in the Z-axis direction, and the front side in FIG. 1 is the front side in the X-axis direction (see the arrow in FIG. 1). Then, the drive part 12 has the Y-axis drive part 12a, the Z-axis drive part 12b, and the X-axis drive part 12c.

  The Y-axis drive portion 12a is provided on the base 11, and moves the apparatus main body 13 in the Y-axis direction (vertical direction) with respect to the base 11 via the Z-axis drive portion 12b and the X-axis drive portion 12c. (Displace). In other words, the Y-axis drive portion 12a is a location for moving the apparatus main body 13 in the Y-axis direction (vertical direction) in the drive unit 12. The Y-axis drive portion 12a has a support column 12d and a Y-axis moving frame 12e. The support column 12d is fixed to the base 11 and extends from the base 11 in the Y-axis direction. The Y-axis moving frame 12e has a frame shape that can surround the support column 12d, and can be moved relative to the Y-axis direction via a Y-axis guide member (not shown). Is attached. The Y-axis moving frame 12e has a movable range in the Y-axis direction with respect to the support column 12d (base 11) at the lowest position in the intraocular pressure measurement unit 20 in an intraocular pressure measurement mode (see FIG. 5A) described later. It is set so that it can be positioned on the (negative side) and the eye characteristic measuring unit 40 can be positioned on the uppermost (positive side) in an eye characteristic measurement mode (see FIG. 5B) described later. Has been.

  In the Y-axis moving frame 12e, although not shown, an elastic member is provided between the Y-axis moving frame 12e and the support column 12d, and a pressing force is applied upward from the elastic member. In this embodiment, the elastic member is formed of a spiral wire, and uses a tension spring that contracts most in an unloaded state and exhibits an elastic force that resists the operation of separating one end and the other end. . That is, the Y-axis moving frame 12e is configured to be suspended from the support column 12d by an elastic member. The Y-axis moving frame 12e is supported on the support column 12d (base 11) via an elastic member in a state where the relative movement direction with respect to the support column 12d (base 11) is defined by the Y-axis guide member in the Y-axis direction. Has been. If the elastic member supports the Y-axis moving frame 12e by applying a pressing force to the support column 12d (base 11) in the Y-axis direction to the Y-axis moving frame 12e, a compression spring is used. It may be used or may have other configurations, and is not limited to this embodiment. The compression spring is constituted by a spiral wire, and exhibits the elastic force that opposes the operation of bringing the one end and the other end close to each other by extending most in an unloaded state. When this compression spring is used, the support column 12d or the base 11 may be configured to support the Y-axis moving frame 12e from below via the compression spring.

  The Y-axis drive portion 12a is provided with a drive force transmission mechanism that applies a moving force to move the Y-axis moving frame 12e in the Y-axis direction with respect to the support column 12d. In the Y-axis drive portion 12a, an upward movement force is applied from the drive force transmission mechanism to the Y-axis movement frame 12e, thereby moving the Y-axis movement frame 12e from the position where the elastic member is balanced to the Y axis direction positive side. By applying a downward moving force to the Y-axis moving frame 12e from the driving force transmission mechanism, the Y-axis moving frame 12e is moved from the position where the elastic members are balanced to the Y-axis direction negative side.

  The Z-axis drive portion 12b is provided on the Y-axis moving frame 12e (Y-axis drive portion 12a), and the apparatus main body 13 is attached to the Y-axis drive portion 12a, that is, the base 11, via the X-axis drive portion 12c. Move (displace) in the Z-axis direction (front-rear direction). In other words, the Z-axis drive portion 12 b is a location for moving the apparatus main body 13 in the Z-axis direction (front-rear direction) in the drive unit 12. The Z-axis drive portion 12b has a Z-axis support base 12f and a Z-axis movement base 12g. The Z-axis support 12f is fixed to the Y-axis moving frame 12e and is moved in the Y-axis direction together with the Y-axis moving frame 12e. The Z-axis support base 12f supports the Z-axis movement base 12g through a Z-axis guide member (not shown) so as to be capable of relative movement in the Z-axis direction. The Z-axis drive portion 12b is provided with a drive force transmission mechanism that applies a moving force that moves the Z-axis moving base 12g in the Z-axis direction with respect to the Z-axis support base 12f. In the Z-axis drive part 12b, the Z-axis moving table 12g is appropriately moved in the Z-axis direction by applying a moving force in the Z-axis direction to the Z-axis moving table 12g from the driving force transmission mechanism.

  The X-axis drive portion 12c is provided on the Z-axis moving base 12g (Z-axis drive portion 12b), and the apparatus body 13 is moved in the X-axis direction (left-right direction) with respect to the Z-axis drive portion 12b, that is, the base 11. Move (displace). In other words, the X-axis drive portion 12 c is configured to move the apparatus main body 13 in the X-axis direction (left-right direction) in the drive unit 12. The X-axis drive portion 12c has an X-axis support base 12h and an X-axis movement base 12i. The X-axis support base 12h is fixed to the Z-axis movement base 12g and is moved in the Z-axis direction together with the Z-axis movement base 12g. The X-axis support base 12h supports the X-axis movement base 12i through an X-axis guide member (not shown) so that relative movement in the X-axis direction is possible. The X-axis drive portion 12c is provided with a drive force transmission mechanism that applies a moving force that moves the X-axis moving base 12i in the X-axis direction with respect to the X-axis support base 12h. In the X-axis drive part 12c, the X-axis moving table 12i is appropriately moved in the X-axis direction by applying a moving force in the X-axis direction to the X-axis moving table 12i from the driving force transmission mechanism. The X-axis moving base 12i is provided with an apparatus main body 13 through an attachment board (not shown) to which an intraocular pressure measurement unit 20 and an eye characteristic measurement unit 40 provided on the inside of the apparatus main body 13 are attached. Is fixed.

  For this reason, the drive unit 12 appropriately drives the Y-axis drive part 12a, the Z-axis drive part 12b, and the X-axis drive part 12c, thereby moving the apparatus main body part 13 in the vertical direction (Y-axis direction) relative to the base 11. , And can be appropriately moved in the front-rear direction (Z-axis direction) and the left-right direction (X-axis direction). In the drive unit 12, although not shown clearly, the Y-axis drive part 12a, the Z-axis drive part 12b, and the X-axis drive part 12c are connected to the control unit 33 (see FIG. 2), respectively. Is driven under the control of the control unit 33. The control unit 33 constitutes an electric control system in the ophthalmologic apparatus 10 and comprehensively controls each unit of the ophthalmologic apparatus 10 by a program stored in a built-in storage unit.

  Although not shown in FIG. 1 for ease of understanding, the ophthalmic apparatus 10 is provided with a cover member that forms the overall outer shape, from the base 11 to the apparatus main body 13 through the drive unit 12. Is covered by the cover member. In FIG. 1, in the drive unit 12, the Y-axis drive portion 12a, the Z-axis drive portion 12b, and the X-axis drive portion 12c are shown stacked in the Y-axis direction, but are completely divided in the Y-axis direction. However, the components are configured to overlap each other when viewed in a direction orthogonal to the Y-axis direction. For this reason, in the drive unit 12, that is, the ophthalmologic apparatus 10, it is possible to appropriately move the apparatus main body 13 with respect to the base 11 while preventing an increase in the height dimension (size as viewed in the Y-axis direction). Has been.

  The apparatus main body 13 is provided with an intraocular pressure measurement unit 20 and an eye characteristic measurement unit 40 inside. The ocular characteristic measurement unit 40 constitutes a first measurement unit having a first set working distance d1 (see FIG. 5B), and the intraocular pressure measurement unit 20 has a second shorter than the first set working distance. A second measuring unit having a set working distance d2 (see FIG. 5A) is configured. Each working distance is a distance that enables the measurement of the eye E to be performed by each measurement unit, and is indicated by a distance (interval) from the tip of each measurement unit to the eye E. The intraocular pressure measurement unit 20 is used when measuring the intraocular pressure of the eye E. The eye characteristic measuring unit 40 measures optical characteristics (eye characteristics) of the eye E, and in this embodiment, the shape of the cornea Ec of the eye E and the eye refractive power (spherical power, astigmatism) of the eye E are measured. Frequency, astigmatic axis angle, etc.).

  In the ophthalmologic apparatus 10 of the present embodiment, in the apparatus main body 13, an optical axis O <b> 1 which will be described later as a main optical axis in the intraocular pressure measurement unit 20 is above a main optical axis O <b> 10 which will be described later in the eye characteristic measurement unit 40 (Y It is provided on the positive side in the axial direction (see FIG. 5). For this reason, in the ophthalmologic apparatus 10, the intraocular pressure measurement unit 20 is basically provided above the eye characteristic measurement unit 40 in the apparatus main body unit 13. Here, what is basically said in the positional relationship between the intraocular pressure measurement unit 20 and the ocular characteristic measurement unit 40 is that the intraocular pressure measurement unit 20 and the ocular characteristic measurement unit 40 are separately configured. Rather, the intraocular pressure measurement unit 20 and the ocular characteristic measurement unit 40 include a part of the intraocular pressure measurement unit 20 and the ocular characteristic measurement unit 40 by crossing a part of one optical system with the other optical system. This is because they are assembled into an integrated structure.

  Next, the optical configuration of the intraocular pressure measurement unit 20 will be described with reference to FIGS. 2 and 3. The intraocular pressure measuring unit 20 is a non-contact type tonometer. As shown in FIGS. 2 and 3, the intraocular pressure measurement unit 20 includes an anterior ocular segment observation optical system 21, an XY alignment index projection optical system 22, a fixation target projection optical system 23, an applanation detection optical system 24, and a Z alignment. An index projection optical system 25 and a Z alignment detection optical system 26 are provided.

  The anterior segment observation optical system 21 is provided for observing the anterior segment of the eye E and XY alignment (alignment in the direction along the XY plane). The anterior ocular segment observation optical system 21 is provided with an anterior ocular segment illumination light source 21a (see FIG. 2), an airflow spray nozzle 21b, an anterior ocular window glass 21c (see FIG. 3), and a chamber on the optical axis O1. A window glass 21d, a half mirror 21e, a half mirror 21g, an objective lens 21f, and a CCD camera 21i are provided. The anterior segment illumination light source 21a is positioned around the anterior segment window glass 21c (see FIG. 2), and a plurality (only two are shown in FIG. 2) are provided to directly illuminate the anterior segment. ing. The airflow spray nozzle 21b is a nozzle for spraying an airflow onto the eye E (anterior eye portion), and is provided in an air compression chamber 34a (see FIG. 3) of the airflow spray mechanism 34 described later. The CCD camera 21i generates an image signal based on an image (anterior eye image or the like) formed on the light receiving surface, and outputs the generated image signal to the control unit 33 (see FIG. 2). The image acquired from the CCD camera 21i is appropriately displayed on the display unit 14 (see FIG. 1) and appropriately output to an external device (not shown) under the control of the control unit 33.

  As shown in FIG. 3, the CCD camera 21i is movable along the optical axis O1 by a focusing drive mechanism 21D. The focusing drive mechanism 21D appropriately moves the CCD camera 21i to focus on the anterior eye part (cornea Ec) of the eye E under the control of the control unit 33 (see FIG. 2). In the focusing drive mechanism 21D, the drive source is shared with a fixation target moving mechanism 41D (see FIG. 4) of the fixation target projection optical system 41 described later. That is, the drive source drives the focusing drive mechanism 21D in an intraocular pressure measurement mode (see FIG. 5A) described later, and a fixation target in an eye characteristic measurement mode (see FIG. 5B) described later. The moving mechanism 41D is driven. The control unit 33 changes the position of the CCD camera 21i on the optical axis O1 in accordance with the position of the intraocular pressure measurement unit 20, that is, the apparatus main body unit 13, via the focusing drive mechanism 21D, thereby changing the eye E to be examined. Focus on the anterior segment of the eye (cornea Ec).

  In the present embodiment, the control unit 33 can displace the CCD camera 21i via the focusing drive mechanism 21D at two positions, the first focal position f1 and the second focal position f2 on the optical axis O1. It is possible. The movement of the CCD camera 21i on the optical axis O1 via the focusing drive mechanism 21D may be switched in two steps between the first focal position f1 and the second focal position f2. The first focal position It may be moved continuously between f1 and the second focal position f2.

  The first focal position f1 is a position at which the intraocular pressure measurement unit 20 (device main body unit 13) can measure the intraocular pressure of the eye E, that is, the anterior eye part (cornea Ec) of the eye E. To the second set working distance d2 (see FIG. 5 (a)), it is a position where the anterior eye portion (cornea Ec) of the eye E is in focus. In this embodiment, the position at which the measurement of the intraocular pressure of the eye E can be performed is 11 mm, which is the distance (interval) from the tip of the airflow spray nozzle 21b to the eye E, that is, the second set working distance d2. (See FIG. 5A).

  The second focal position f2 corresponds to the anterior eye portion (cornea Ec) of the eye E when the intraocular pressure measurement unit 20 (apparatus body 13) is positioned sufficiently away from the eye E (subject). This is the position where the camera is focused. As will be described later, when switching from the eye characteristic measurement mode (measurement mode by the eye characteristic measurement unit 40) to the intraocular pressure measurement mode (measurement mode by the intraocular pressure measurement unit 20), the intraocular pressure measurement unit 20 (device) The main body 13) is first moved in the Y-axis direction to a height position corresponding to the eye E, and then moved in the Z-axis direction to approach the eye E. Such movement is performed in order to prevent the airflow spray nozzle 21b (the tip thereof) that is extremely close to the eye E from coming into contact with the eye E by mistake. Alternatively, in the intraocular pressure measurement mode, when the subject eye E to be measured is switched between the left and right eyes of the subject, the intraocular pressure measurement unit 20 (device main body unit 13) is first retracted from the position where one of the intraocular pressures is measured. (Z-axis direction negative side), moving in the left-right direction (X-axis direction), and performing the alignment while moving in the direction approaching the other eye E to be examined. Such an operation is performed to prevent the tip of the airflow spray nozzle 21b of the tonometry part 20 from accidentally contacting the subject (its nose, etc.).

  In this embodiment, the control unit 33 is positioned in the Z-axis direction (front-rear direction) of the apparatus main body 13 (intraocular pressure measurement unit 20) with respect to the base 11, that is, the drive unit 12 (its Z-axis drive portion 12b). The position of the CCD camera 21i is switched between the first focal position f1 and the second focal position f2 according to the control position. This is because the interval between the intraocular pressure measurement unit 20 and the eye E to be examined is roughly determined by the position of the apparatus main body 13 (intraocular pressure measurement unit 20) with respect to the base 11. In the focusing drive mechanism 21D, the drive source is shared with the fixation target moving mechanism 41D (see FIG. 4) of the fixation target projection optical system 41 described later. The index moving mechanism 43D (see FIG. 4) of the index projection optical system 43 (light receiving optical system 44) may be shared with the drive source, and is not limited to the present embodiment.

  In this anterior ocular segment observation optical system 21, an anterior ocular segment image of the subject eye E is illuminated by a CCD camera 21i while illuminating the subject eye E (the anterior segment) with an anterior segment illumination light source 21a (see FIG. 2). get. The anterior eye part image (the light beam) passes through the airflow blowing nozzle 21b and passes through the anterior eye part window glass 21c (including a glass plate 34b described later), the chamber window glass 21d, the half mirror 21g, and the half mirror 21e. Then, it is focused by the objective lens 21f and formed on the CCD camera 21i (its light receiving surface). The CCD camera 21i (anterior ocular segment observation optical system 21) outputs a signal based on reception of the formed anterior ocular segment image to the control unit 33 (see FIG. 2). The control unit 33 causes the display unit 14 (see FIG. 1) to appropriately display the anterior segment image acquired by the CCD camera 21i (anterior segment observation optical system 21). For this reason, the anterior ocular segment observation optical system 21 functions as a second observation optical system in the intraocular pressure measurement unit 20, that is, the second measurement unit. This anterior ocular segment observation optical system 21 (second observation optical system) is set to a higher magnification than an observation optical system 42 as a first observation optical system to be described later in the eye characteristic measurement unit 40 (first measurement unit). May be. This is because, in the intraocular pressure measurement unit 20 (second measurement unit), the measurement result of the intraocular pressure of the eye E is likely to be affected by a decrease in alignment accuracy. This is because it is required to increase the accuracy of alignment compared to the above.

  Further, in the anterior ocular segment observation optical system 21, as described later, the reflected light from the cornea Ec of the XY alignment index light projected onto the eye E by the XY alignment index projection optical system 22 is converted into a CCD camera 21i (its light receiving surface). To proceed. Specifically, in the anterior ocular segment observation optical system 21, the reflected light flux passes through the inside of the airflow blowing nozzle 21b, passes through the chamber window glass 21d, the half mirror 21g, and the half mirror 21e, and reaches the objective lens 21f. . Then, in the anterior ocular segment observation optical system 21, the reflected light beam is converged by the objective lens 21f and advanced to the CCD camera 21i. Then, on the CCD camera 21i (its light receiving surface), a bright spot image is formed at a position corresponding to the positional relationship in the XY direction between the apparatus main body 13 (intraocular pressure measurement unit 20) and the cornea Ec. The CCD camera 21i (anterior ocular segment observation optical system 21) can output a signal based on reception of the formed bright spot image to the control unit 33 (see FIG. 2). The bright spot image of the XY alignment index light is formed on the cornea Ec of the eye E to be examined. For this reason, the control part 33 can acquire the image (the data) of the anterior eye part (cornea Ec) in which the bright spot image was formed, and the anterior eye part (in which the bright spot image was formed on the display part 14) An image of the cornea Ec) can be displayed as appropriate. The display unit 14 also displays an alignment auxiliary mark generated by image generation means (not shown) in an overlapping manner.

  The XY alignment index projection optical system 22 projects the index light onto the cornea Ec of the eye E from the front. The index light is a position adjustment with respect to the intraocular pressure measurement unit 20 of the eye E (the anterior eye portion (cornea Ec)) viewed in a direction along the XY plane (hereinafter also referred to as XY direction), so-called XY. It has a function that enables alignment in the direction. The index light also has a function that enables detection of the deformation amount (degree of deformation (applanation)) of the cornea Ec of the eye E. The XY alignment index projection optical system 22 includes an XY alignment light source 22a, a condenser lens 22b, an aperture stop 22c, a pinhole plate 22d, a dichroic mirror 22e, and a projection lens 22f. The half mirror 21e is shared. The XY alignment light source 22a is a light source that emits infrared light. The projection lens 22f is disposed on the optical path of the XY alignment index projection optical system 22 so that the focal point coincides with the pinhole plate 22d. In the XY alignment index projection optical system 22, infrared light emitted from the XY alignment light source 22a passes through the aperture stop 22c while being focused by the condenser lens 22b, and reaches the pinhole plate 22d (its hole). And proceed. In the XY alignment index projection optical system 22, the light beam that has passed through the pinhole plate 22d (its hole) is reflected by the dichroic mirror 22e and travels to the projection lens 22f, and the progressed infrared light is projected by the projection lens 22f. It advances to the half mirror 21e as a parallel light beam. Then, in the XY alignment index projection optical system 22, the parallel light beam is advanced on the optical axis O <b> 1 of the anterior ocular segment observation optical system 21 by being reflected by the half mirror 21 e. The parallel luminous flux passes through the half mirror 21g and the chamber window glass 21d, proceeds to the inside of the airflow spray nozzle 21b, and passes through the airflow spray nozzle 21b to the eye E as XY alignment index light. It reaches. Although not shown, the XY alignment index light is reflected on the surface of the cornea Ec so as to form a bright spot image at an intermediate position between the cornea vertex Ea of the cornea Ec and the center of curvature of the cornea Ec. The aperture stop 22c is provided at a position conjugate with the corneal vertex Ea of the cornea Ec with respect to the projection lens 22f.

  The fixation target projection optical system 23 projects (presents) the fixation target onto the eye E to be examined. The fixation target projection optical system 23 includes a fixation target light source 23a and a pinhole plate 23b. The fixation target projection optical system 23 shares the XY alignment index projection optical system 22, the dichroic mirror 22e, and the projection lens 22f, and anterior ocular segment observation optics. The system 21 and the half mirror 21e are shared. The fixation target light source 23a is a light source that emits visible light. In the fixation target projection optical system 23, the fixation target light emitted from the fixation target light source 23a is advanced to the pinhole plate 23b (the hole) and passes through the pinhole plate 23b (the hole). Then, the light passes through the dichroic mirror 22e and advances to the projection lens 22f. The fixation target light (the light beam) is made substantially parallel light by the projection lens 22f, travels to the half mirror 21e, and is reflected by the half mirror 21e, whereby the optical axis O1 of the anterior ocular segment observation optical system 21 is obtained. Go on top. The luminous flux passes through the half mirror 21g and the chamber window glass 21d, travels into the airflow spray nozzle 21b, passes through the airflow spray nozzle 21b, and reaches the eye E to be examined. The fixation target projection optical system 23 fixes the line of sight of the subject by causing the subject to gaze at the fixation target projected onto the eye E as a fixation target.

  As shown in FIG. 3, the applanation detection optical system 24 receives light reflected by the cornea Ec of the XY alignment index light projected onto the eye E by the XY alignment index projection optical system 22, and the surface of the cornea Ec. The amount of deformation (applanation) is detected. The applanation detection optical system 24 includes a lens 24a, a pinhole plate 24b, a sensor 24c, and a half mirror 21g provided on the optical path of the anterior ocular segment observation optical system 21. When only the surface of the cornea Ec is flattened, the lens 24a condenses the light reflected by the cornea Ec of the XY alignment index light in the central hole of the pinhole plate 24b. The pinhole plate 24b is provided with the central hole positioned at the above-described condensing position by the lens 24a. The sensor 24c is a light receiving sensor capable of detecting the amount of light, and outputs a signal corresponding to the amount of received light. In the present embodiment, a photodiode is used. The sensor 24c (applanation detection optical system 24) outputs a signal corresponding to the received light amount to the control unit 33.

  As described above, the reflected light beam of the XY alignment index light reflected by the surface (corneal surface) of the cornea Ec of the eye E passes through the air blowing nozzle 21b, passes through the chamber window glass 21d, and passes through the half mirror 21g. To. In the applanation detection optical system 24, a part thereof is reflected by the half mirror 21g, travels to the lens 24a, converges by the lens 24a, and travels to the pinhole plate 24b. Here, in the eye E, the surface of the cornea Ec is deformed and gradually flattened by the airflow spraying mechanism 34 (see FIG. 1 and the like), which will be described later, blowing airflow from the airflow spraying nozzle 21b toward the cornea Ec. It will be in a state. At that time, in the applanation detection optical system 24, when the surface of the cornea Ec is flattened according to the setting described above, the entire reflected light beam that has traveled reaches the sensor 24c through the hole of the pinhole plate 24b, and other states Then, the sensor reaches the sensor 24c while being partially blocked by the pinhole plate 24b. For this reason, the applanation detection optical system 24 can detect that the surface of the cornea Ec has been flattened (applanation) by detecting the time when the amount of light received by the sensor 24c becomes maximum. As a result, the applanation detection optical system 24 can detect the shape (applanation) of the surface of the cornea Ec that has been deformed by spraying fluid, and the sensor 24c can detect the reflected light (reflected light) from the cornea Ec for the detection. It functions as a light receiving portion that receives a light beam.

  As shown in FIG. 2, the Z alignment index projection optical system 25 projects the alignment index light (alignment index parallel light beam) in the Z-axis direction obliquely onto the cornea Ec of the eye E to be examined. The Z alignment index projection optical system 25 includes a Z alignment light source 25a, a condenser lens 25b, an aperture stop 25c, a pinhole plate 25d, and a projection lens 25e on the optical axis O2. The light source 25a for Z alignment is a light source that emits infrared light (for example, wavelength 860 nm). The aperture stop 25c is provided at a position conjugate with the corneal vertex Ea of the cornea Ec with respect to the projection lens 25e. The projection lens 25e is disposed with its focal point coincident with the pinhole plate 25d (the hole). In the Z alignment index projection optical system 25, infrared light (its light beam) emitted from the Z alignment light source 25a is condensed by the condenser lens 25b, passes through the aperture stop 25c, and proceeds to the pinhole plate 25d. To do. In this Z alignment index projection optical system 25, the light beam that has passed through the pinhole plate 25d (the hole) is advanced to the projection lens 25e, and is advanced to the cornea Ec as parallel light by the projection lens 25e. The infrared light (the light beam (Z alignment index light)) is reflected on the surface of the cornea Ec so as to form a bright spot image located inside the eye E.

  The Z alignment detection optical system 26 receives the reflected light from the cornea Ec of the Z alignment index light from a direction symmetric with respect to the optical axis O1 of the anterior ocular segment observation optical system 21, and the apparatus main body 13 (intraocular pressure measurement). Part 20) and the cornea Ec in the Z-axis direction are detected. The Z alignment detection optical system 26 includes an imaging lens 26a, a cylindrical lens 26b, and a sensor 26c on the optical axis O3. The cylindrical lens 26b has power in the Y-axis direction. The sensor 26c is a light receiving sensor that can detect the light receiving position on the light receiving surface, and can be configured using a line sensor or PSD. In this embodiment, a line sensor is used. The sensor 26 c is connected to the Z alignment detection correction unit 32.

  In the Z alignment detection optical system 26, the reflected light beam projected from the alignment index light by the Z alignment index projection optical system 25 and reflected from the surface of the cornea Ec proceeds to the imaging lens 26a. In the Z alignment detection optical system 26, the reflected light beam is converged by the imaging lens 26a, travels to the cylindrical lens 26b, and is condensed in the Y-axis direction by the cylindrical lens 26b to form a bright spot image on the sensor 26c. . The sensor 26c is in a conjugate positional relationship with respect to the above-described bright spot image formed on the inside of the eye E by the Z alignment index projection optical system 25 and the imaging lens 26a in the XZ plane, and is Y- In the Z plane, the corneal apex Ea is in a conjugate positional relationship with the imaging lens 26a and the cylindrical lens 26b. That is, the sensor 26c has a conjugate relationship with the aperture stop 25c (the magnification at this time is set so that the image of the aperture stop 25c is smaller than the size of the sensor 26c), and the cornea Ec has shifted in the Y-axis direction. However, the reflected light beam on the surface of the cornea Ec efficiently enters the sensor 26c. The sensor 26 c (Z alignment detection optical system 26) outputs a signal based on reception of the formed bright spot image to the Z alignment detection correction unit 32.

  As shown in FIG. 3, the airflow blowing mechanism 34 has an air compression chamber 34a, and is provided with an air compression drive unit 34d (see FIG. 1). The air compression drive unit 34d has a piston that can move inward of the air compression chamber 34a and a drive unit that moves the piston. In the present embodiment, the device main body unit 13 includes an intraocular pressure measurement unit. 20 (its optical system) is provided above. The air compression drive unit 34d is driven under the control of the control unit 33 (see FIG. 2) to compress the air in the air compression chamber 34a. An air blowing nozzle 21b is attached to the air compression chamber 34a via a transparent glass plate 34b, and a chamber window glass 21d is provided to face the nozzle. For this reason, the air compression chamber 34a is prevented from interfering with the above-described function in the anterior ocular segment observation optical system 21. The air compression chamber 34a is provided with a pressure sensor 34c that detects the pressure of the air compression chamber 34a. Although not shown, the pressure sensor 34c is connected to the control unit 33 (see FIG. 2), and outputs a signal corresponding to the detected pressure to the control unit 33. In the airflow blowing mechanism 34, the air compression driving unit 34 d compresses the air in the air compression chamber 34 a under the control of the control unit 33, so that the airflow is directed from the airflow blowing nozzle 21 b toward the cornea Ec of the eye E to be examined. Can be sprayed. Further, in the airflow blowing mechanism 34, the pressure when the airflow is blown from the airflow blowing nozzle 21b can be acquired by detecting the pressure in the air compression chamber 34a with the pressure sensor 34c. In the airflow blowing mechanism 34, instead of providing the pressure sensor 34c, a change in pressure with respect to time may be set as a predetermined characteristic in the airflow to be blown.

  The intraocular pressure measurement unit 20 includes a driver (drive mechanism) for performing lighting control of the anterior segment illumination light source 21a, the XY alignment light source 22a, the fixation target light source 23a, and the Z alignment light source 25a. A controller 33 (see FIG. 2) is connected to the driver. Therefore, the intraocular pressure measurement unit 20 appropriately turns on the anterior segment illumination light source 21a, the XY alignment light source 22a, the fixation target light source 23a, and the Z alignment light source 25a under the control of the control unit 33. In the intraocular pressure measurement unit 20, as described above, the CCD camera 21i is appropriately moved on the optical axis O1 via the focusing drive mechanism 21D under the control of the control unit 33, and output from the CCD camera 21i. An image generation process based on the image signal is performed, and the generated image is appropriately displayed on the display unit 14.

  Next, a schematic operation when measuring the intraocular pressure of the eye E using the above-described intraocular pressure measurement unit 20 will be described. In addition, the following operation | movement in the intraocular pressure measurement part 20 is performed under control of the control part 33 (refer FIG. 2). First, the power switch of the ophthalmic apparatus 10 is turned on, and an operation for performing measurement using the intraocular pressure measurement unit 20 is performed on the display unit 14. Then, the intraocular pressure measurement unit 20 sets the intraocular pressure measurement mode (see FIG. 5A) as will be described later, and then the anterior ocular segment illumination light source 21a, XY alignment light source 22a, fixation target light source 23a, and Z. The alignment light source 25a is appropriately turned on. At this time, the intraocular pressure measurement unit 20 may repeatedly blink each of the light sources 21a, 23a, and 25a at different periods, and may identify which light source is the light.

  As shown in FIG. 3, the intraocular pressure measurement unit 20 lights the fixation target light source 23 a of the fixation target projection optical system 23, thereby projecting the fixation target onto the eye E to be examined. The subject's line of sight is fixed. Further, the intraocular pressure measurement unit 20 lights the XY alignment light source 22a of the XY alignment index projection optical system 22 to project a parallel light beam onto the cornea Ec. In the intraocular pressure measurement unit 20, the reflected light beam reflected by the cornea Ec is received by the CCD camera 21 i of the anterior ocular segment observation optical system 21 and the sensor 24 c of the applanation detection optical system 24. Further, as shown in FIG. 2, the intraocular pressure measuring unit 20 lights the Z alignment light source 25a of the Z alignment index projection optical system 25 to project a parallel light beam for alignment in the Z-axis direction onto the cornea Ec. . In the intraocular pressure measurement unit 20, the reflected light beam reflected by the cornea Ec is received by the sensor 26 c of the Z alignment detection optical system 26.

  In the intraocular pressure measurement unit 20, the anterior segment illumination light source 21a of the anterior segment observation optical system 21 is turned on to illuminate the anterior segment of the subject eye E, and the anterior segment image of the subject eye E is displayed as a CCD camera. An image is formed on 21i. The intraocular pressure measurement unit 20 displays the anterior eye image of the eye E on which the luminescent spot image of the XY alignment index light is formed and the alignment auxiliary mark on the display unit 14 although they are not clearly shown. Let The examiner operates the operation unit displayed on the display unit 14 while looking at the display unit 14, thereby moving the apparatus main body unit 13 up and down and left and right so that the bright spot image appears in the screen of the display unit 14. Align so that. Further, in the intraocular pressure measurement unit 20, the Z alignment detection / correction unit 32 is based on the light reception signal of the sensor 26 c of the Z alignment detection optical system 26 and the calculation result of the XY alignment detection unit 31, and the apparatus main body unit 13 and the cornea Ec. Is calculated in the Z-axis direction. In the intraocular pressure measurement unit 20, the drive unit 12 is controlled based on the position in the XY direction obtained from the anterior segment observation optical system 21 and the calculation result output from the Z alignment detection correction unit 32 under the control of the control unit 33. That is, by appropriately driving the Y-axis drive portion 12a, the Z-axis drive portion 12b, and the X-axis drive portion 12c, the apparatus body 13 is moved in the vertical direction (Y-axis direction) and the front-rear direction (Z-axis direction) with respect to the base 11. ) And the right and left direction (X-axis direction) as appropriate, and auto alignment (automatic alignment adjustment) is performed.

  In the intraocular pressure measurement unit 20, when the auto alignment is completed, the control unit 33 activates the airflow blowing mechanism 34 to blow an airflow from the airflow blowing nozzle 21b toward the cornea Ec of the eye E to be examined. Then, in the eye E, the surface of the cornea Ec is deformed and gradually becomes flat (applanation). In the process in which the cornea Ec is gradually flattened (applanation), the amount of light received by the sensor 24c of the applanation detection optical system 24 becomes maximum when the surface of the cornea Ec is flattened (applanation). . Therefore, in the intraocular pressure measurement unit 20, the control unit 33 determines that the surface of the cornea Ec is flat (applanation) based on the change in the amount of light received by the sensor 24c. That is, the applanation detection optical system 24 (sensor 24c) can detect the applanation of the cornea Ec. In the intraocular pressure measurement unit 20, the control unit 33 obtains the intraocular pressure of the eye E (calculates the intraocular pressure value) based on the output from the pressure sensor 34c (the pressure of the blown airflow) and calculates the intraocular pressure. The result is displayed on the display unit 14. In addition, in the control part 33, based on the time from the time of detecting that the surface of the cornea Ec was made flat (applanation) from the time of starting the blowing of the airflow by the airflow blowing nozzle 21b (airflow blowing mechanism 34), What calculates | requires the intraocular pressure of the to-be-tested eye E (it calculates an intraocular pressure value) may be sufficient.

  Next, the optical configuration of the eye characteristic measurement unit 40 will be described with reference to FIG. The eye characteristic measurement unit 40 measures the shape of the cornea Ec of the eye E and the eye refractive power (spherical power, astigmatism power, astigmatic axis angle, etc.) of the eye E. As shown in FIG. 4, the eye characteristic measuring unit 40 includes a fixation target projection optical system 41, an observation optical system 42, an eye refractive power measurement ring-shaped index projection optical system 43, a light receiving optical system 44, and an alignment light projection system 45. With. The fixation target projection optical system 41 projects the target on the fundus oculi Ef (see FIGS. 2 and 3) of the eye E to fixate and cloud the eye E to be examined. The observation optical system 42 observes the anterior eye part (cornea Ec) of the eye E to be examined. The ring-shaped index projection optical system 43 for measuring eye refractive power projects a pattern light beam as a ring-shaped index for measuring eye refractive power onto the fundus oculi Ef of the eye E to measure the eye refractive power of the eye E. To do. The light receiving optical system 44 causes the imaging element 44d described later to receive the eye refractive power measurement ring-shaped index image reflected from the fundus oculi Ef of the eye E. The eye refractive power measurement ring-shaped index projection optical system 43 and the light receiving optical system 44 together with the observation optical system 42 and a corneal shape measurement ring-shaped index projection light source 46A, 46B, 46C described later, measure the corneal shape and eye refractive power. Configure the optical system. The alignment light projection system 45 projects the index light toward the eye E to detect the alignment state in the XY direction. The optical system of the eye characteristic measuring unit 40 is provided with a working distance detection optical system for detecting a working distance between the eye E to be examined and the apparatus main body 13 although not shown.

  The fixation target projection optical system 41 includes, on the optical axis O11, a fixation target light source 41a, a collimator lens 41b, an index plate 41c, a relay lens 41d, a mirror 41e, a dichroic mirror 41f, a dichroic mirror 41g, and an objective lens 41h. . The index plate 41c is provided with a target for fixing the eye E to be inspected and fogged. The fixation target light source 41a, the collimator lens 41b, and the index plate 41c constitute a fixation target unit 41U, and the fixation target projection optical system 41 is fixed by the fixation target moving mechanism 41D so as to fixate and cloud the eye E to be examined. It is possible to move integrally along the optical axis O11. Note that the positions where the dichroic mirror 41g and the objective lens 41h are provided are on the main optical axis O10 in the eye characteristic measurement unit 40 described later.

  In this fixation target projection optical system 41, visible light is emitted from a fixation target light source 41a, and the visible light is converted into a parallel light beam by a collimator lens 41b, and then transmitted through an index plate 41c to be a target light beam. In the fixation target projecting optical system 41, the target light beam is reflected by the mirror 41e after passing through the relay lens 41d, passes through the dichroic mirror 41f, and advances to the dichroic mirror 41g. In the fixation target projecting optical system 41, the target light flux is reflected by the dichroic mirror 41g onto the main optical axis O10 in the eye characteristic measuring unit 40, and is advanced to the eye E through the objective lens 41h. The fixation target projection optical system 41 fixes the line of sight of the subject by causing the subject to focus on the target luminous flux (fixation target) projected onto the eye E as a fixation target. Further, the fixation target projection optical system 41 moves the fixation target unit 41U from a state in which the subject gazes as a fixation target to a position where the focus is not achieved, so that the eye E is in a cloudy state. .

  The observation optical system 42 has an illumination light source (not shown), and has a half mirror 42a, a relay lens 42b, an imaging lens 42c, and an image sensor 42d on the main optical axis O10. The objective lens 41h and the dichroic mirror 41g are shared. The image sensor 42d is a two-dimensional solid-state image sensor, and a CMOS image sensor is used in this embodiment.

  In this observation optical system 42, the anterior eye portion (cornea Ec) of the eye E is illuminated with the illumination light beam emitted from the illumination light source, and the illumination light beam reflected by the anterior eye portion is acquired by the objective lens 41h. In the observation optical system 42, the reflected illumination light beam is imaged on the imaging element 42d (its light receiving surface) by the imaging lens 42c through the objective lens 41h, the dichroic mirror 41g and the half mirror 42a, the relay lens 42b, and the like. Let The imaging element 42d outputs an image signal based on the acquired image to the control unit 33 (see FIG. 2). The control unit 33 causes the display unit 14 to display an image of the anterior segment (cornea Ec) based on the input image signal. Therefore, in the observation optical system 42, an image of the anterior segment (cornea Ec) can be formed on the image sensor 42d (its light receiving surface), and the image of the anterior segment can be displayed on the display unit 14. it can. Note that the illumination light source of the observation optical system 42 is turned off when the refractive power is measured after the alignment is completed. Therefore, the observation optical system 42 functions as a first observation optical system in the eye characteristic measurement unit 40, that is, the first measurement unit. Even if this observation optical system 42 (first observation optical system) is set to a lower magnification than the anterior ocular segment observation optical system 21 as the second observation optical system in the intraocular pressure measurement unit 20 (second measurement unit). Good. This is because the eye characteristic measurement unit 40 (first measurement unit) is not required to increase the alignment accuracy unlike the intraocular pressure measurement unit 20 (second measurement unit).

  An eye refractive power measurement ring-shaped index projection optical system 43 includes an eye refractive power measurement light source 43a, a lens 43b, a conical prism 43c, a ring index plate 43d, a lens 43e, a bandpass filter 43f, a pupil ring 43g, and a perforated prism 43h. And the fixed prism projection optical system 41, the dichroic mirror 41f, the dichroic mirror 41g, and the objective lens 41h. The eye refractive power measurement light source 43a and the pupil ring 43g are arranged at an optically conjugate position, and the ring index plate 43d and the fundus oculi Ef of the eye E are arranged at an optically conjugate position. The eye refractive power measurement light source 43a, the lens 43b, the conical prism 43c, and the ring index plate 43d constitute an index unit 43U. The index unit 43U projects an eye refractive power measurement ring index by the index moving mechanism 43D. The optical system 43 can be moved integrally along the optical axis O13.

  In the eye refractive power measurement ring index projection optical system 43, the light beam emitted from the eye refractive power measurement light source 43a is converted into a parallel light beam by the lens 43b and travels to the ring index plate 43d through the conical prism 43c. The luminous flux passes through the ring-shaped pattern portion formed on the ring index plate 43d and becomes a pattern luminous flux as a ring-shaped index for eye refractive power measurement. In this ring-shaped index projection optical system 43 for measuring eye refractive power, the pattern light flux is advanced to the perforated prism 43h through the lens 43e, the band pass filter 43f and the pupil ring 43g, and is reflected by the reflecting surface of the perforated prism 43h. The light is reflected and travels through the rotary prism 43i to the dichroic mirror 41f. Then, in the ring-shaped index projection optical system 43 for measuring the eye refractive power, the pattern light beam is reflected by the dichroic mirror 41g after being reflected by the dichroic mirror 41f, so as to travel on the main optical axis O10 in the eye characteristic measuring unit 40. Then, in the ring-shaped index projection optical system 43 for measuring eye refractive power, the pattern light beam is imaged on the fundus oculi Ef (see FIGS. 2 and 3) of the eye E by the objective lens 41h.

  The eye refractive power measurement ring index projection optical system 43 is provided with corneal shape measurement ring index projection light sources 46A, 46B, and 46C on the front side of the objective lens 41h. The corneal shape measurement ring-shaped index projection light sources 46A, 46B, and 46C are concentrically provided with respect to the main optical axis O10 at a predetermined distance from the eye E (cornea Ec) on the ring pattern 47. A ring-shaped index light for corneal shape measurement is projected onto the optometry E (cornea Ec). The corneal shape measurement ring-shaped index light is projected onto the cornea Ec of the eye E, thereby forming a corneal shape measurement ring-shaped index light on the cornea Ec. The ring-shaped index for measuring the corneal shape (the light beam) is reflected on the cornea Ec of the eye E to be imaged on the image sensor 42d by the observation optical system 42 described above. Therefore, in the observation optical system 42, the display unit 14 can display an image (image) of a ring-shaped index for corneal shape measurement so as to overlap the image of the anterior segment (cornea Ec).

  The light receiving optical system 44 includes a hole 44a of the perforated prism 43h, a mirror 44b, a lens 44c, and an imaging device 44d, and shares the fixation target projection optical system 41, the objective lens 41h, the dichroic mirror 41g, and the dichroic mirror 41f. In addition, the ring-shaped index projection optical system 43 for measuring eye refractive power and the rotary prism 43i are shared. The image pickup device 44d is a two-dimensional solid-state image pickup device, and a CCD (charge coupled device) image sensor is used in this embodiment. This image sensor 44d is linked to the index unit 43U of the eye refractive power measurement ring-shaped index projection optical system 43 by the index moving mechanism 43D of the eye refractive power measurement ring-shaped index projection optical system 43, and receives the light receiving optical system. It is possible to move along 44 optical axes O14.

  In the light receiving optical system 44, a pattern reflected light beam guided to the fundus oculi Ef (see FIGS. 2 and 3) by the eye refractive power measurement ring-shaped index projection optical system 43 and reflected by the fundus oculi Ef is reflected by the objective lens 41h. The light is condensed, reflected by the dichroic mirror 41g, then reflected by the dichroic mirror 41f, and advanced to the rotary prism 43i. In the light receiving optical system 44, the reflected pattern reflected light beam travels through the rotary prism 43i to the hole 44a of the holed prism 43h and passes through the hole 44a. In the light receiving optical system 44, the pattern reflected light beam that has passed through the hole 44a is reflected by the mirror 44b, and a pattern reflected light beam, that is, a ring-shaped index for eye refractive power measurement is formed on the image pickup device 44d (its light receiving surface) by the lens 44c. Let me image. The imaging element 44d outputs an image signal based on the acquired image to the control unit 33 (see FIG. 2). The control unit 33 causes the display unit 14 (see FIG. 1) to display an image of an eye refractive power measurement ring index based on the input image signal. For this reason, in the light receiving optical system 44, an image of a ring-shaped index for measuring eye refractive power can be formed on the image sensor 44d (its light-receiving surface), and the ring-shaped index for measuring eye refractive power is displayed on the display unit 14. An image can be displayed.

  The alignment light projection system 45 includes an LED 45a, a pinhole 45b, and a lens 45c, shares the observation optical system 42 and the half mirror 42a, and shares the fixation target projection optical system 41, the dichroic mirror 41g, and the objective lens 41h. . In this alignment light projection system 45, the light beam from the LED 45a is converted into an alignment index light beam through the pinhole 45b (the hole) and reflected by the half mirror 42a through the lens 45c, so that the main optical axis in the eye characteristic measurement unit 40 is obtained. Advance over O10. In the alignment light projection system 45, the alignment index light beam is advanced to the objective lens 41h through the dichroic mirror 41g, and is projected as an alignment index light beam toward the cornea Ec of the eye E through the objective lens 41h. The alignment light projection system 45 has a function of automatically aligning the apparatus main body 13 with respect to the eye E by projecting an alignment index light beam toward the cornea Ec of the eye E. The alignment index light beam projected as parallel light toward the eye E is reflected by the cornea Ec of the eye E, and a bright spot image as an alignment index image is projected on the image sensor 42d by the observation optical system 42. The When this bright spot image is positioned within an alignment mark formed by an optical system (not shown), the alignment is completed.

  The eye characteristic measurement unit 40 controls lighting of the fixation target light source 41a, the illumination light source of the observation optical system 42, the eye refractive power measurement light source 43a, the LED 45a, and the corneal shape measurement ring-shaped index projection light sources 46A, 46B, and 46C. And a control unit 33 (see FIG. 2) is connected to the driver. Therefore, the eye characteristic measurement unit 40, under the control of the control unit 33, projects the fixation target light source 41a, the illumination light source of the observation optical system 42, the eye refractive power measurement light source 43a, the LED 45a, and the corneal shape measurement ring-shaped index projection. The light sources 46A, 46B, and 46C are appropriately turned on. Further, as described above, the eye characteristic measurement unit 40 moves the fixation target unit 41U integrally along the optical axis O11 via the fixation target moving mechanism 41D under the control of the control unit 33, and moves the index. The index unit 43U is moved integrally along the optical axis O13 via the mechanism 43D, and the imaging element 44d is moved along the optical axis O14. Further, as described above, the eye characteristic measurement unit 40 performs an image generation process based on the image signals output from the image sensor 42d and the image sensor 44d under the control of the control unit 33, and the generated image is displayed. Displayed appropriately on the display unit 14.

  Next, a schematic view of measuring the shape of the cornea Ec of the eye E and the eye refractive power (spherical power, astigmatism power, astigmatic axis angle, etc.) of the eye E using the eye characteristic measuring unit 40 described above. The operation will be described. In addition, the following operation | movement in the eye characteristic measurement part 40 is performed under control of the control part 33 (refer FIG. 2). First, the power switch of the ophthalmologic apparatus 10 is turned on, and an operation for performing measurement using the eye characteristic measurement unit 40 is performed on the display unit 14. Then, in the eye characteristic measurement unit 40, as described later, after the eye characteristic measurement mode (see FIG. 5B) is set, the illumination light source is turned on in the observation optical system 42, and the anterior eye part ( An image of the cornea Ec) is displayed. Then, the examiner operates the operation unit displayed on the display unit 14 so that the pupil Ep (see FIG. 8) of the eye E is positioned within the screen of the display unit 14, thereby moving the apparatus main body unit 13. The apparatus main body 13 is roughly aligned with respect to the eye E by moving it vertically and horizontally. In addition, the eye characteristic measurement unit 40 (control unit 33) can detect the pupil Ep from the anterior eye image based on the image signal output from the image sensor 42d. The detection of the pupil Ep can be performed, for example, by previously storing a shape to be recognized as the pupil Ep in the image of the anterior eye part and detecting the shape to be recognized based on the contrast in the image. . Therefore, in the eye characteristic measurement unit 40, for example, when the subject eye E to be measured is switched left and right, the pupil Ep based on the image while moving the apparatus main body 13 in the left and right direction according to the switching. , And the apparatus main body 13 (eye characteristic measurement unit 40) is moved with the detected pupil Ep as a target position, whereby the above-described general alignment can be automatically performed.

  Then, in the eye characteristic measurement unit 40, the observation optical system 42 causes the display unit 14 to display a bright spot image as an alignment index image. Thereafter, the eye characteristic measurement unit 40 starts alignment detection based on the alignment light projection system 45 and the working distance detection optical system (not shown). That is, in the eye characteristic measuring unit 40, the apparatus main body 13 is moved in the vertical direction (Y-axis direction) and the front-rear direction (Z-axis) with respect to the base 11 so that the bright spot image as the alignment index image is positioned in the alignment mark. Direction) and left and right direction (X-axis direction) as appropriate, and auto alignment (automatic alignment adjustment) is performed. Thereby, in the eye characteristic measurement part 40, the automatic alignment with respect to the vertex of the cornea Ec of the eye E of the apparatus main body part 13 is completed.

  Then, the eye characteristic measuring unit 40 turns on the corneal shape measurement ring-shaped index projection light sources 46A, 46B, and 46C of the eye-refractive-index ring-shaped index projection optical system 43, and uses the corneal shape measurement ring-shaped index as the cornea. Project to Ec. Then, the control unit 33 measures the shape of the cornea Ec from the image of the corneal shape measurement ring-shaped index projected onto the cornea Ec based on the image displayed on the display unit 14 (image signal from the imaging element 42d). To do. Since the details of the measurement of the shape of the cornea Ec are known, the description thereof is omitted. The control unit 33 can measure the spherical power, the cylindrical power, and the shaft angle as the eye refractive power by a known method. The configuration of the eye refractive power measurement unit is the same as that disclosed in JP-A-2002-253506, but is not limited to this configuration. Thus, the control unit 33 performs measurement of the corneal shape and measurement of eye refractive power (optical characteristics). In addition, the control part 33 stores a calculation result etc. in a memory | storage part (illustration is abbreviate | omitted) suitably.

  In the ophthalmologic apparatus 10, in the present embodiment, in the apparatus main body 13, the tonometry part 20 is basically provided above the eye characteristic measurement part 40, and the tonometry part 20 and the eye characteristic measurement part 40 are provided. It is attached to the mounting base and fixed to each other. In other words, in the ophthalmologic apparatus 10, in the apparatus main body 13, the intraocular pressure measurement unit 20 and the eye characteristic measurement unit 40 are integrated to eliminate the need to change the positional relationship. For this reason, the mounting base, that is, the intraocular pressure measurement unit 20 and the eye characteristic measurement unit 40 (device main body unit 13) attached thereto, are connected to the drive unit 12, that is, the Y-axis drive part 12a, the Z-axis drive part 12b, and the X-axis drive part 12c. Accordingly, the base 11 is appropriately moved in the vertical direction (Y-axis direction), the front-rear direction (Z-axis direction), and the left-right direction (X-axis direction). In the ophthalmic apparatus 10, the apparatus main body 13 (mounting base) is moved with respect to the base 11 by the drive unit 12 (Y-axis drive part 12 a, Z-axis drive part 12 b and X-axis drive part 12 c). Each of the intraocular pressure measurement unit 20 and the eye characteristic measurement unit 40 can be moved to a position corresponding to the eye E (face of the subject) fixed by the chin rest 15 and the forehead support 16. (See FIG. 5).

  For this reason, in the ophthalmologic apparatus 10, the intraocular pressure measurement is performed by moving the apparatus main body 13 (mounting base) in the vertical direction (Y-axis direction) with respect to the base 11 by the Y-axis drive portion 12a of the drive unit 12. The eye E can be positioned on the extension line of the optical axis O1 of the anterior ocular segment observation optical system 21 of the unit 20, and the intraocular pressure measurement unit 20 can be made to correspond to the height position of the eye E (FIG. 5A). )reference). In the ophthalmologic apparatus 10, as shown in FIG. 5A, the anterior ocular segment of the intraocular pressure measuring unit 20 is moved in the front-rear direction (Z-axis direction) by the Z-axis drive portion 12 b of the drive unit 12. It is assumed that the tip of the airflow spray nozzle 21b of the observation optical system 21 is located at the second set working distance d2 from the eye E (the corneal vertex Ea). The second set working distance d2 is 11 mm in this embodiment. This state is a measurement mode by the intraocular pressure measurement unit 20, that is, an intraocular pressure measurement mode.

  Further, in the ophthalmologic apparatus 10, the apparatus main body part 13 (mounting base) is moved in the vertical direction (Y-axis direction) by the Y-axis drive part 12 a of the drive part 12 with respect to the base 11, thereby the eye characteristic measurement part. The eye E can be positioned on the extended line of the main optical axis O10 of 40, and the eye characteristic measuring unit 40 can correspond to the height position of the eye E (see FIG. 5B). Then, in the ophthalmologic apparatus 10, as shown in FIG. 5B, the front end of the eye characteristic measurement unit 40 (main book) is moved by the Z-axis drive portion 12 b of the drive unit 12 in the front-rear direction (Z-axis direction). In the embodiment, the ring pattern 47) is located at the first set working distance d1 from the eye E to be examined. The front end of the eye characteristic measuring unit 40 refers to a structure that is closest to the subject in the eye characteristic measuring unit 40, and is a ring pattern 47 in this embodiment. The first set working distance d1 is about 80 mm in this embodiment. This state is a measurement mode by the eye characteristic measurement unit 40, that is, an eye characteristic measurement mode.

  Accordingly, in this embodiment, the ophthalmologic apparatus 10 is configured so that the front end (airflow spray nozzle 21b) of the intraocular pressure measurement unit 20 is positioned on the positive side in the Z-axis direction (the ring pattern 47) with respect to the front end (ring pattern 47). It is displaced to the subject side). This is due to the following. In the ophthalmologic apparatus 10, in the intraocular pressure measurement mode with the above-described configuration, as shown in FIG. 5A, a ring pattern 47 serving as the front end of the eye characteristic measurement unit 40 is placed in front of the subject's nose and mouth. To position. In the ophthalmologic apparatus 10, the intraocular pressure measurement unit 20 and the eye characteristic measurement unit 40 are integrated, and the positional relationship is not changed. Therefore, in the ophthalmologic apparatus 10, for example, when the front end of the intraocular pressure measurement unit 20 and the front end of the eye characteristic measurement unit 40 are set at the same position when viewed in the Z-axis direction (front-rear direction), in the intraocular pressure measurement mode, the ring The pattern 47 comes into contact with the subject's nose and mouth, or the ring pattern 47 gives the subject a cramped feeling even if it does not come into contact. In view of this, in the ophthalmologic apparatus 10, the front end (airflow spray nozzle 21b) of the intraocular pressure measurement unit 20 is displaced from the front end (ring pattern 47) of the eye characteristic measurement unit 40 to the positive side in the Z-axis direction. In the intraocular pressure measurement mode, a space is secured in front of the subject's nose and mouth.

  Accordingly, in this embodiment, the ophthalmologic apparatus 10 uses the eye characteristic measuring unit 40 to perform the measurement from the eye E (its cornea vertex Ea) to the front end of the eye characteristic measuring unit 40 (in this example, The first set working distance d1 to the ring pattern 47) is set to 75 mm or more (in this embodiment, about 80 mm). This is due to the following. The first set working distance d1 is a distance that enables the eye characteristic measuring unit 40 to perform the measurement of the eye E. When the eye characteristic measuring unit 40 performs the measurement, the eye E ( It becomes a reference position when moving in the Z-axis direction according to the state. For this reason, in the eye characteristic measurement unit 40, a movement width for moving from the first set working distance d1 to the positive side and the negative side in the Z-axis direction is set, and in this embodiment, the movement width is ± 20 mm. It is said that. In the ophthalmologic apparatus 10, as described above, the front end (airflow spray nozzle 21 b) of the intraocular pressure measurement unit 20 is displaced more to the Z axis direction positive side than the front end (ring pattern 47) of the eye characteristic measurement unit 40. . Thereby, in the ophthalmologic apparatus 10, when the eye characteristic measurement mode is set, as shown in FIG. The air blowing nozzle 21b that is the front end of the portion 20 is located. For this reason, in the ophthalmologic apparatus 10, when the first setting working distance d1 in the eye characteristic measurement unit 40 is small, when moving to the Z axis direction positive side (subject side) with the above movement width, There is a possibility that the front end (airflow spray nozzle 21 b) of the intraocular pressure measurement unit 20 may interfere with the chin rest 15. In other words, in the ophthalmologic apparatus 10, in order to be able to move the eye characteristic measurement unit 40 from the first set working distance d1 to the Z axis direction positive side (subject side) with the above-described movement width, It is necessary to increase the first set working distance d1. For this reason, in the ophthalmologic apparatus 10, the first setting working distance d <b> 1 is set to 75 mm or more in the eye characteristic measurement unit 40, and is set to about 80 mm in this embodiment. Note that the setting of the first set working distance d1 can be performed by adjusting the setting of the optical characteristics of each optical member in the eye characteristic measuring unit 40. For this reason, in the ophthalmologic apparatus 10, even if the front end (airflow spray nozzle 21b) of the intraocular pressure measurement unit 20 is displaced to the positive side in the Z-axis direction from the front end (ring pattern 47) of the eye characteristic measurement unit 40, the ocular characteristics When the measurement mode is set, the front end (airflow spray nozzle 21 b) of the intraocular pressure measurement unit 20 is reliably prevented from interfering with the chin rest 15.

  In addition to this, in the ophthalmologic apparatus 10, as shown in FIG. 6A, the apparatus main body 13 is provided with a height position detection unit 48 that detects that a predetermined height position HL has been reached. The height position HL is set from the viewpoint of preventing the airflow blowing nozzle 21b of the intraocular pressure measurement unit 20 from interfering with the forehead portion 16. In the example shown in FIG. 6 (a), the height position HL has a sufficient distance between the airflow spray nozzle 21b and the forehead portion 16, but the distance may be set as appropriate. It is not limited to this embodiment. When the apparatus main body 13 reaches the height position HL, the height position detector 48 outputs a signal indicating that to the controller 33 (see FIG. 2). When the control unit 33 acquires the signal from the height position detection unit 48, the control unit 33 is in the intraocular pressure measurement mode, or when the intraocular pressure measurement unit 20 is on the positive side in the Z-axis direction (the subject) If it exists on the side), the movement of the apparatus main body 13 upward is stopped. The predetermined front and rear positions are set from the viewpoint of preventing the airflow blowing nozzle 21b from interfering with the forehead portion 16 when viewed in the Z-axis direction.

  Then, when the control unit 33 acquires the above-described signal from the height position detection unit 48, the control unit 33 stops the upward movement of the apparatus main body 13 and moves the apparatus main body 13 upward (Y-axis direction positive side). Control according to the moved situation is executed. For example, when the apparatus main body 13 is moved upward based on an operation performed on the display unit 14, the control according to the situation may cause the display unit 14 to move further upward. It is possible to display that it is not possible. The control according to the situation is, for example, when the movement for switching from the intraocular pressure measurement unit 20 to the eye characteristic measurement unit 40 is performed, the device main body unit 13 is moved backward (Z-axis) in the front-rear direction. For example, the apparatus main body 13 may be moved upward after being retracted (moved) in the negative direction). Furthermore, when the control unit 33 acquires the signal from the height position detection unit 48 while performing automatic alignment in the intraocular pressure measurement unit 20, the control unit 33 re-detects the eye E. This is because when the automatic alignment in the tonometry part 20 is performed, the apparatus main body part 13 has reached the height position HL, and thus the detection of the eye E as the alignment reference has failed. By meaning.

  In addition, when the power switch of the ophthalmic apparatus 10 is turned on, the control unit 33 determines whether or not the above-described signal is output from the height position detection unit 48 before the apparatus main body unit 13 is moved. To do. And the control part 33 performs the movement of the apparatus main body part 13 suitably, when the above-mentioned signal is not output from the height position detection part 48. FIG. In addition, when the above-described signal is output from the height position detection unit 48, the control unit 33 does not move the apparatus main body unit 13 upward and performs control according to the situation. The control according to the situation indicates, for example, that when the operation of moving the apparatus main body 13 upward on the display unit 14 is performed, the display unit 14 cannot be moved further upward. Can be mentioned. Further, the control according to the situation is, for example, when the movement for switching from the intraocular pressure measurement unit 20 to the ocular characteristic measurement unit 40 is performed, the apparatus main body unit 13 is moved backward in the front-rear direction (Z-axis direction negative). And the apparatus main body 13 is moved upward after being moved back (moved). Thereby, in the ophthalmologic apparatus 10, for example, the switching operation is performed from the intraocular pressure measurement unit 20 to the eye characteristic measurement unit 40, and the power switch is turned off in a state where the height position detection unit 48 outputs the above signal. Even when the power switch is turned on again, the apparatus main body 13 can be moved while reliably preventing the airflow blowing nozzle 21b from interfering with the forehead portion 16 when the power switch is turned on again. In the example shown in FIG. 6A, the height position detection unit 48 is provided in the apparatus main body 13, but actually controls the position of the apparatus main body 13 in the height direction, that is, the Y-axis direction. It may be provided in the Y-axis drive part 12a of the drive part 12, and may be provided in another place, and is not limited to the present embodiment.

  Further, in the ophthalmologic apparatus 10, as shown in FIG. 6B, the apparatus main body 13 is provided with a front position detection unit 49 that detects that a predetermined front position FL has been reached. The front position FL is set from the viewpoint of preventing the airflow spray nozzle 21b of the intraocular pressure measurement unit 20 from interfering with the forehead portion 16 in the eye characteristic measurement mode. In this embodiment, the front position FL is a position where the distance between the tip of the airflow spray nozzle 21b and the forehead portion 16 is 1 mm. The forward position FL may be set as appropriate by setting the distance between the airflow spray nozzle 21b and the forehead portion 16 and is not limited to this embodiment. When the apparatus main body 13 reaches the front position FL, the front position detection unit 49 outputs a signal indicating that to the control unit 33 (see FIG. 2). When the control unit 33 acquires the signal from the front position detection unit 49 in the eye characteristic measurement mode, the control unit 33 moves the apparatus main body unit 13 forward (Z-axis direction positive side (subject side)). Stop that.

  When the control unit 33 acquires the above signal from the front position detection unit 49 in the eye characteristic measurement mode, the control unit 33 stops moving the apparatus main body 13 forward and moves the apparatus main body 13 forward. Control according to the moved situation is executed. For example, when the apparatus main body 13 is moved forward based on an operation performed on the display unit 14, the control according to the situation means that the display unit 14 may move further forward. It is possible to display that it is not possible. Further, when the power switch of the ophthalmic apparatus 10 is turned on, the control unit 33 determines whether or not the above-described signal is output from the front position detection unit 49 before the movement of the apparatus main body unit 13 is executed. . And the control part 33 performs the movement of the apparatus main body part 13 suitably, when the above-mentioned signal is not output from the front position detection part 49. FIG. In addition, when the above-described signal is output from the front position detection unit 49, the control unit 33 does not move the apparatus main body unit 13 forward, and performs control according to the situation. The control according to the situation means that, for example, when an operation for moving the apparatus main body 13 forward is performed on the display unit 14, the display unit 14 displays that no further forward movement is possible. Can be mentioned. In the example shown in FIG. 6B, the front position detection unit 49 is provided in the apparatus main body 13, but a drive unit that actually controls the position of the apparatus main body 13 in the front-rear direction, that is, the Z-axis direction. 12 may be provided in the Z-axis drive portion 12b or may be provided in another place, and is not limited to the present embodiment.

  In this ophthalmologic apparatus 10, generally, after measuring the shape of the cornea Ec of the eye E and the eye refractive power (spherical power, astigmatism power, astigmatic axis angle, etc.) of the eye E by the eye characteristic measuring unit 40, The intraocular pressure of the eye E is measured by the intraocular pressure measurement unit 20. In the ophthalmologic apparatus 10, as described above, the control unit 33 (see FIG. 2) controls the operation of each unit based on the operation performed on the display unit 14.

  When the power switch is turned on, the ophthalmologic apparatus 10 displays an intraocular pressure switching icon for the intraocular pressure measurement mode and an ocular characteristic switching icon for the eye characteristic measurement mode on the display unit 14. In addition, in this display unit 14, if it is possible to select and switch between the intraocular pressure measurement mode and the ocular characteristic measurement mode, instead of displaying the intraocular pressure switching icon and the ocular characteristic measurement mode, the display unit 14 The switching icon may be displayed, an icon in another format may be displayed, and the present invention is not limited to the configuration of the present embodiment. Then, in order to measure the shape of the cornea Ec of the eye E and the eye refractive power (spherical power, astigmatism power, astigmatic axis angle, etc.) of the eye E by the eye characteristic measuring unit 40 first, the eye characteristics of the display unit 14 are measured. It is assumed that the switching icon is touched (selected).

  Then, in the ophthalmologic apparatus 10, the Y-axis drive portion 12a, the Z-axis drive portion 12b, and the X-axis drive portion 12c of the drive unit 12 are appropriately driven to enter the eye characteristic measurement mode (see FIG. 5B). That is, in the ophthalmologic apparatus 10, as shown in FIG. 5B, the eye E is positioned on the extension line of the main optical axis O <b> 10 of the eye characteristic measurement unit 40 and the fixation target projection optics of the eye characteristic measurement unit 40 is used. Assuming that the objective lens 41h of the system 41 is located at the first set working distance d1 from the eye E, the eye characteristic measuring unit 40 is made to correspond to the eye E. In the ophthalmologic apparatus 10, the shape of the cornea Ec of the eye E and the eye refractive power (spherical power, astigmatism power, astigmatic axis angle, etc.) of the eye E are measured by the above-described operation of the eye characteristic measurement unit 40. . Thereafter, in order to measure the intraocular pressure of the eye E, it is assumed that the intraocular pressure switching icon on the display unit 14 is touched (selected).

  Then, in the ophthalmologic apparatus 10, the Y-axis drive portion 12a, the Z-axis drive portion 12b, and the X-axis drive portion 12c of the drive unit 12 are appropriately driven to enter an intraocular pressure measurement mode (see FIG. 5A). Here, in the ophthalmic apparatus 10, first, the apparatus main body 13 is moved to the Y axis direction negative side, and the intraocular pressure measurement unit 20 is set to a height position corresponding to the eye E to be examined. At this time, in the ophthalmologic apparatus 10, the position of the CCD camera 21i on the optical axis O1 is set as the second focal position f2 (see FIG. 3) via the focusing drive mechanism 21D. Thereby, in the ophthalmologic apparatus 10, the image of the eye E (the anterior eye portion (cornea Ec)) can be appropriately displayed on the display unit 14. Thereafter, in the ophthalmologic apparatus 10, the apparatus main body 13 is moved to the positive side in the Z-axis direction to bring the intraocular pressure measurement unit 20 closer to the eye E to be examined, and as shown in FIG. Assuming that the tip of the nozzle 21b is located at the second set working distance d2 from the eye E, the intraocular pressure measurement unit 20 is made to correspond to the eye E. At this time, in the ophthalmologic apparatus 10, the position of the CCD camera 21i on the optical axis O1 is moved to the first focal position f1 (see FIG. 3) via the focusing drive mechanism 21D. Thereby, in the ophthalmologic apparatus 10, the image of the eye E (the anterior eye portion (cornea Ec)) can be appropriately displayed on the display unit 14. In the ophthalmologic apparatus 10, the intraocular pressure of the eye E is measured by the above-described operation of the intraocular pressure measurement unit 20.

  Thereby, in the ophthalmologic apparatus 10, the eye characteristic measurement unit 40 measures the shape of the cornea Ec of the eye E and the eye refractive power (spherical power, astigmatism power, astigmatic axis angle, etc.) of the eye E, and measures the intraocular pressure. The intraocular pressure of the eye E can be measured by the unit 20.

  Next, a characteristic configuration of the ophthalmologic apparatus 10 of the present embodiment according to the present invention will be described with reference to FIGS. 7 shows a state in which the eye characteristic measurement unit 40 is set to the first set working distance d1, and FIG. 10 shows a state in which the intraocular pressure measurement unit 20 is set to the second set working distance d2. However, the difference in position with respect to the subject based on the difference between the first set working distance d1 and the second set working distance d2 is shown in an easy-to-understand manner. Not what you want.

  In the ophthalmologic apparatus 10, when an eye characteristic is measured using the eye characteristic measurement unit 40 (see FIG. 4), an image of the anterior eye part (cornea Ec) is formed on the image sensor 42 d (its light receiving surface) by the observation optical system 42. By forming the image, an image of the anterior segment is acquired, and the image (its data) is output to the control unit 33. The ophthalmologic apparatus 10 can display an image acquired by the observation optical system 42 (imaging element 42d) on the display unit 14 under the control of the control unit 33 (see FIG. 2) (see FIG. 8).

  In the ophthalmologic apparatus 10, the control unit 33 can detect the position of the pupil Ep in the eye E (cornea Ec) in the input image (its data). The detection of the pupil Ep can be performed by storing in advance the shape to be recognized as the pupil Ep in the anterior eye image and detecting the shape to be recognized based on the contrast in the image. Thereby, the control part 33 can detect the area | region which shows the pupil Ep, and its center position in the image of the anterior eye part. The detection of the position of the pupil Ep may be performed by another method as long as it is detected in the image (its data) acquired by the observation optical system 42 (image sensor 42d). It is not limited to the method.

  In the ophthalmologic apparatus 10, it is possible to perform schematic alignment of the apparatus body 13 with respect to the eye E using a function of detecting the position of the pupil Ep. An example of this schematic alignment will be described using the situation shown in FIG. 7 in which the eye characteristic measurement unit 40 measures both eyes in order. In the situation shown in FIG. 7, first, the left eye of the subject (the subject eye EL in the case of individual examination) is set as the measurement target (see FIG. 7A), and then the right eye of the subject (individually) In this case, the eye to be examined is ER) (see FIG. 7B). In this case, after measuring the eye to be examined EL, the control unit 33 moves the apparatus main body 13 (eye characteristic measurement unit 40) to the eye to be examined ER side (X-axis direction negative side) so that the eye ER to be examined is a measurement target. To perform approximate alignment to a position corresponding to the eye ER to be examined. At this time, in the image (the data) input to the control unit 33, the eye to be examined EL moves to the right side as shown in FIG. 8A, and eventually the observation optical as shown in FIG. 8B. The subject eye ER enters the field of view of the system 42 (on the screen of the display unit 14). Then, as shown in FIG. 8C, when the eye ER to be examined enters the center direction of the image (its data), the pupil Ep of the eye ER to be examined can be detected. Then, the pupil Ep is detected, and the apparatus main body 13 (eye characteristic measuring unit 40) is moved with the detected pupil Ep as a target position, whereby the automatic approximate alignment is completed. Thereby, in the eye characteristic measurement part 40 (control part 33), as above-mentioned, the automatic alignment with respect to the vertex of the cornea Ec of the to-be-tested eye E of the apparatus main body part 13 can be performed, and the to-be-tested eye ER is measured. It becomes possible.

  At this time, since the first set working distance d1 is large in the eye characteristic measuring unit 40, as shown in FIG. 7, the apparatus main body 13 (the tip thereof) does not interfere with the subject. Therefore, the apparatus main body 13 can be moved in the X-axis direction without moving in the Z-axis direction. Here, since the observation optical system 42 is provided for measurement by the eye characteristic measurement unit 40, the eye E to be examined is set to the first set working distance d1 of the eye characteristic measurement unit 40. Is properly focused. For this reason, in the eye characteristic measurement unit 40 (control unit 33), erroneous detection of the pupil Ep such as detection of an unrelated item as the pupil Ep or detection of the pupil Ep is basically not caused.

  In addition, in the ophthalmologic apparatus 10, the control unit 33 can store the positions in the XYZ directions. In this embodiment, the XYZ position in each direction is determined by using the number of pulses of a pulse motor as a drive source in the Y-axis drive portion 12a, the Z-axis drive portion 12b, and the X-axis drive portion 12c of the drive unit 12. It is controlled. Therefore, the control unit 33 counts the number of pulses from each reference position in each direction of XYZ, and stores the count number, thereby storing the position in each direction of XYZ. This storage is performed by storing in a storage unit built in the control unit 33 or a storage unit provided outside the control unit 33. Using this function, the control unit 33 completes the alignment to measure the position of the apparatus main body 13 in each of the XYZ directions and the eye ER to be measured when the alignment is completed to measure the eye E to be examined. The position of the apparatus main body 13 in each direction of XYZ at the time is stored. Then, the control unit 33 obtains the binocular interval dm (see FIG. 7 and the like), which is the interval between the eye EL to be examined and the eye ER to be obtained, by obtaining the difference in position in both directions of both XYZ. The binocular interval dm is stored. Further, the control unit 33 may obtain the binocular interval dm by obtaining the difference between the positions in both X-axis directions. The storage of the position in each direction of XYZ may be performed based on the change in the position of the apparatus main body 13 (eye characteristic measurement unit 40), and is appropriately performed according to the configuration of the drive unit 12 and the like. However, the present invention is not limited to the configuration of this embodiment.

  Further, in the ophthalmologic apparatus 10, the control unit 33 acquires an image of the anterior segment (cornea Ec) acquired by the observation optical system 42 (first observation optical system) of the eye characteristic measurement unit 40 (first measurement unit) (data thereof). ) To obtain the binocular distance dm. This is because the binocular interval dm is used for switching the left and right eye E during measurement by the intraocular pressure measuring unit 20 (second measuring unit) as will be described later. This is because the position of the optometry E may be grasped. As a method of obtaining using this image (its data), for example, using the center position of the pupil Ep of both eyes E in the image, and the corneal vertex Ea of the cornea Ec of both eyes E in the image (that) Position). As described above, since the control unit 33 can detect the center position of the pupil Ep in the image (its data) as described above, this function may be used. The corneal vertex Ea (its position) is determined by the control unit 33 in the position (data) of the bright spot image formed by the alignment light projection system 45, that is, on the XY plane of the bright spot image. It can be detected by determining the position. This is because the bright spot image formed by the alignment light projection system 45 is formed on an axis passing through the corneal apex Ea and the center of curvature of the cornea Ec. Thus, as described above, obtaining the binocular distance dm using the position of the apparatus main body 13 in each of the XYZ directions at the time when the alignment is completed is based on the position of the apparatus main body 13. The binocular distance dm is obtained from the cornea vertex Ea of the optometry E.

  In addition, in the ophthalmologic apparatus 10, the control unit 33 includes an image of the anterior segment (cornea Ec) acquired by the observation optical system 42 (first observation optical system) of the eye characteristic measurement unit 40 (first measurement unit). It is possible to detect the amount of deviation (size and direction) between the main optical axis O10 of the eye characteristic measurement unit 40 and the eye E to be detected using the data. As the position of the eye E, for example, the center position of the pupil Ep and the corneal apex Ea (its position) can be obtained from the image (its data) as described above. This is because the amount of deviation (size and direction) from the position of the optical axis O1 of the measurement unit 20 may be obtained. Similarly, the control part 33 is the image (the data) of the anterior eye part (cornea Ec) acquired by the anterior eye part observation optical system 21 (second observation optical system) of the intraocular pressure measurement part 20 (second measurement part). It is possible to detect the amount of deviation (size and direction) between the optical axis O1 of the intraocular pressure measurement unit 20 and the eye E to be examined. The control unit 33 can use the deviation amount as a correction value when determining the position of the apparatus main body 13 in each of the XYZ directions, and corrects the deviation amount when the apparatus main body 13 is moved. Can be used as a value.

  Next, the second measuring unit, which is executed in the control unit 33, is automatically moved from a position suitable for one eye E to a position suitable for the other eye E as a second measuring unit. The left and right eye switching operation process for executing the left and right eye switching operation method in the (intraocular pressure measurement unit 20) will be described with reference to FIG. FIG. 9 is a flowchart showing left / right eye switching operation processing (left / right eye switching operation method) executed by the control unit 33 in the present embodiment. This left / right eye switching operation process (left / right eye switching operation method) is executed by the control unit 33 based on a program stored in a storage unit built in the control unit 33 or a storage unit provided outside the control unit 33. To do.

  The left and right eye switching operation processing (left and right eye switching operation method) basically includes both eye E when measuring the left and right eye E of the subject using the eye characteristic measuring unit 40 (first measuring unit). Between the left and right eye E during the measurement by the intraocular pressure measurement unit 20 (second measurement unit) is performed using the obtained binocular interval dm. . For this reason, in the left-right eye switching operation process (left-right eye switching operation method), it is necessary to measure the left and right eye E of the subject using the eye characteristic measurement unit 40 (first measurement unit) first. It becomes. Note that the measurement using the eye characteristic measurement unit 40 (first measurement unit) performed earlier is performed immediately before the right and left eye E of the subject is measured by the intraocular pressure measurement unit 20 (second measurement unit). The present invention is not limited to this, and may have been performed on the subject in the past, and is not limited to the present embodiment. In this case, the binocular interval dm when performed on the subject in the past may be stored in association with the subject.

  Below, each step (each process) of the flowchart of FIG. 9 as this right-and-left eye switching operation process (left-right eye switching operation method) is demonstrated. In the flowchart of FIG. 9, the eye characteristic measurement unit 40 (first measurement unit) is used to measure the eye to be examined EL (left eye) and then the eye to be examined ER (right eye). An example is shown in which the measurement unit 20 (second measurement unit) is used to measure the subject eye ER (right eye) and then the subject eye EL (left eye). Note that the shift from the measurement in the eye characteristic measurement unit 40 (first measurement unit) to the measurement in the intraocular pressure measurement unit 20 (second measurement unit) is the left and right eye in the eye characteristic measurement unit 40 (first measurement unit). When the measurement is completed, it may be switched automatically, or may be performed by touching the intraocular pressure switching icon as described above. Further, the order of the left and right when measuring the left and right eye E may be any, and is not limited to this embodiment. Furthermore, in the measurement by the eye characteristic measurement unit 40 (first measurement unit) and the intraocular pressure measurement unit 20 (second measurement unit), the switching of the left and right eye E is performed by an operation to execute. There may be. This flowchart (left and right eye switching operation processing (left and right eye switching operation method)) is started when an operation for starting measurement of the eye EL to be examined is performed by the eye characteristic measurement unit 40 (first measurement unit).

  In step S1, automatic alignment of the eye characteristic measurement unit 40 (first measurement unit) with respect to the eye to be examined EL is executed, and the process proceeds to step S2. In this step S1, in the eye characteristic measurement unit 40, based on the alignment light projection system 45 and the working distance detection optical system (not shown), the bright spot image as the alignment index image formed on the eye EL to be examined is included in the alignment mark. The apparatus main body 13 is appropriately moved with respect to the base 11 so as to be positioned in the automatic alignment. As a result, the eye EL to be examined is positioned on the main optical axis O10 of the eye characteristic measurement unit 40, and the tip of the eye characteristic measurement unit 40 is located at the first set working distance d1 from the eye to be examined. The eye characteristic measurement unit 40 is set to a position suitable for the eye to be examined EL.

  In step S2, following the execution of automatic alignment of the eye characteristic measurement unit 40 (first measurement unit) with respect to the eye EL in step S1, the eye characteristic of the eye EL to be examined by the eye characteristic measurement unit 40 (first measurement unit) Measurement is performed, and the process proceeds to step S3. In step S2, as described above, the eye characteristic measurement unit 40 performs the measurement of the eye characteristic of the eye EL to be examined. In step S2 of the present embodiment, the characteristic measurement unit 40 measures the corneal shape and the eye refractive power (optical characteristics) of the eye to be examined.

  In step S3, following the measurement of the eye characteristics of the eye EL by the eye characteristic measurement unit 40 (first measurement unit) in step S2, automatic alignment of the eye characteristic measurement unit 40 (first measurement unit) with respect to the eye EL is performed. Execute and proceed to step S4. In step S3, as in step S1, automatic alignment is performed on the eye to be examined EL. As a result, the eye EL to be examined is positioned on the main optical axis O10 of the eye characteristic measurement unit 40, and the tip of the eye characteristic measurement unit 40 is located at the first set working distance d1 from the eye to be examined. The eye characteristic measurement unit 40 is set to a position suitable for the eye to be examined EL. In step S3, when the automatic alignment is completed, the position (coordinate position) of the apparatus main body 13 (eye characteristic measurement unit 40) in the completed state in the XYZ axis direction is stored. This position may be stored only in the position in the X-axis direction. That is, in this step S3, since the measurement of the eye EL is completed and the process proceeds to the measurement of the eye ER, the eye to be examined is stored in order to store the exact position of the eye EL just before the transition. Perform automatic alignment with EL. As described above, correction is performed using the image (the data) of the anterior segment (cornea Ec) acquired by the observation optical system 42 (first observation optical system) of the eye characteristic measurement unit 40 (first measurement unit). When using the amount of deviation as a quantity, or when obtaining the binocular interval dm using the image (the data), the center position of the pupil Ep or the bright spot image (corneal vertex Ea) in the image (the data) It is only necessary to detect the position of the position and move to the position.

  In step S4, following the execution of automatic alignment of the eye characteristic measurement unit 40 (first measurement unit) with respect to the eye EL in step S3, the left / right switching of the eye characteristic measurement unit 40 (first measurement unit) with respect to both eyes E is performed. Move and go to step S5. In step S4, since the eye characteristics of the eye EL to be examined have been measured and the eye characteristics of the eye ER to be examined have not yet been measured, the apparatus body 13 is placed on the eye ER side (X-axis direction negative side). To perform a rough alignment with a position corresponding to the eye ER to be examined. That is, in step S4, the apparatus main body 13 is moved to the eye ER side (X-axis direction negative side) while executing detection control of the eye ER (its pupil Ep) in the image acquired by the observation optical system 42 (image sensor 42d). ). In step S4, when the pupil Ep of the eye ER to be examined is detected, the apparatus main body 13 is moved (rough alignment) so that the pupil Ep (the center thereof) is positioned on the main optical axis O10 of the eye characteristic measuring unit 40. Let That is, in step S4, the pupil Ep of the eye ER to be examined is detected, and the apparatus main body 13 (eye characteristic measuring unit 40) is moved with the detected pupil Ep (center thereof) as a target position. Thereby, the left-right switching movement of the eye E (in this example, from the eye EL to the eye ER) is completed.

  In step S5, following the left-right switching movement of the eye characteristic measurement unit 40 (first measurement unit) with respect to both eyes E in step S4, automatic alignment of the eye characteristic measurement unit 40 (first measurement unit) with respect to the eye ER is performed. Execute and proceed to step S6. In this step S5, automatic alignment with respect to the eye ER to be examined is performed as in steps S1 and S3. Thus, the eye ER to be examined is positioned on the main optical axis O10 of the eye characteristic measurement unit 40, and the tip of the eye characteristic measurement unit 40 is located at the first set working distance d1 from the eye ER to be examined. The eye characteristic measurement unit 40 is set to a position suitable for the eye ER to be examined. In step S5, when the automatic alignment is completed, the position (coordinate position) of the apparatus main body 13 (eye characteristic measurement unit 40) in the completed state in the XYZ axis direction is stored. This position may be stored only in the position in the X-axis direction.

  In step S6, following the execution of the automatic alignment for the eye ER of the eye characteristic measurement unit 40 (first measurement unit) in step S5, the binocular interval dm between the eyes E (the eye EL to be examined and the eye ER to be examined). And the process proceeds to step S7. In this step S6, both eyes of both eyes E (the eye to be examined EL and the eye to be examined ER) are based on the position of the eye to be examined EL stored in step S3 and the position of the eye to be examined ER stored in step S5. The distance dm is calculated and the binocular distance dm is stored. For this reason, in step S <b> 6, the binocular interval dm is obtained from the corneal vertex Ea of both eyes E using the position of the apparatus main body 13. As described above, both images using the image (the data) of the anterior segment (cornea Ec) acquired by the observation optical system 42 (first observation optical system) of the eye characteristic measurement unit 40 (first measurement unit) are used. When obtaining the eye interval dm, the center position of the pupil Ep of both eyes E may be used, or the cornea vertex Ea (the position) of the cornea Ec of both eyes E may be used. Here, the intraocular pressure measurement unit 20 (second measurement unit) of the present embodiment measures the intraocular pressure of the eye E, and applies light to the corneal apex Ea (the position) of the cornea Ec of the eye E. Since measurement is performed with the axis O1 coincident, it is desirable to obtain the binocular interval dm using the corneal vertex Ea (the position) of the cornea Ec of both eyes E.

  In step S7, following the calculation of the binocular distance dm of both eyes E in step S6, the eye characteristics of the eye ER to be examined are measured by the eye characteristics measuring unit 40 (first measuring unit), and the process proceeds to step S8. . In step S7, as described above, the eye characteristic measurement unit 40 performs the measurement of the eye characteristic of the eye ER to be examined. In step S7 of the present embodiment, the characteristic measurement unit 40 measures the cornea shape and eye refractive power (optical characteristics) of the eye ER to be examined.

  In step S8, following the measurement of the eye characteristic of the eye ER to be examined by the eye characteristic measurement unit 40 (first measurement unit) in step S7, switching control from the eye characteristic measurement mode to the intraocular pressure measurement mode is performed, and step S9 is performed. Proceed to In step S8, as described above, the Y-axis drive portion 12a, the Z-axis drive portion 12b, and the X-axis drive portion 12c of the drive unit 12 are appropriately driven to enter the eye characteristic measurement mode. Switch to. In this example, the optical axis O1 of the intraocular pressure measurement unit 20 from the state in which the eye ER to be examined is positioned on the main optical axis O10 of the eye characteristic measurement unit 40 (see FIGS. 5B and 7B). The state is shifted to the state where the eye ER to be examined is positioned (see FIGS. 5A and 10A).

  In step S9, following the switching control from the eye characteristic measurement mode to the intraocular pressure measurement mode in step S8, automatic alignment of the eye pressure measurement unit 20 (second measurement unit) with respect to the eye ER is executed, and the process proceeds to step S10. move on. In step S9, the tonometry part 20 uses the base 11 based on the position of the eye ER in the XY direction obtained from the anterior eye observation optical system 21 and the calculation result output from the Z alignment detection correction part 32. In contrast, the apparatus main body 13 is appropriately moved to perform automatic alignment. Then, the apparatus main body 13 is moved to the positive side in the Z-axis direction, the intraocular pressure measurement unit 20 approaches the eye ER to be examined, and the tip of the airflow spray nozzle 21b is moved from the eye ER to the second set working distance d2. It is supposed to be located in As a result, the eye ER to be examined is positioned on the optical axis O1 of the tonometry part 20, and the tip of the tonometry part 20 is located at the second set working distance d2 from the eye ER to be examined. The pressure measuring unit 20 is set to a position suitable for the eye ER to be examined.

  In step S10, following the execution of automatic alignment for the eye ER of the eye pressure measurement unit 20 (second measurement unit) in step S9, the intraocular pressure of the eye ER to be examined by the eye pressure measurement unit 20 (second measurement unit) is determined. Measurement is performed, and the process proceeds to step S11. In step S10, as described above, the intraocular pressure of the eye ER to be examined is measured by the intraocular pressure measurement unit 20.

  In step S11, following the measurement of the intraocular pressure of the eye ER to be examined by the intraocular pressure measurement unit 20 (second measurement unit) in step S10, automatic alignment of the eye pressure measurement unit 20 (second measurement unit) with respect to the eye ER to be examined is performed. Execute and proceed to step S12. In this step S11, automatic alignment with respect to the eye ER to be examined is performed as in step S9. As a result, the eye ER to be examined is positioned on the optical axis O1 of the tonometry part 20, and the tip of the tonometry part 20 is located at the second set working distance d2 from the eye ER to be examined. The pressure measuring unit 20 is set to a position suitable for the eye ER to be examined. In step S11, when the automatic alignment is completed, the position (coordinate position) of the apparatus main body 13 (intraocular pressure measurement unit 20) in the completed state in the XYZ axis directions is stored. This position may be stored only in the position in the X-axis direction. In step S11, in the image (data) of the anterior segment (cornea Ec) acquired by the anterior segment observation optical system 21 (second observation optical system) of the tonometry unit 20 (second measurement unit). It is good also as what moves to the position which can detect the center position of the pupil Ep, or the position of the bright spot image (corneal vertex Ea). This is because, in step S11, as described later, the reference position for moving the apparatus main body 13 (intraocular pressure measurement unit 20) is determined using the binocular distance dm in step S12. In this case, the control unit 33 includes the center position of the pupil Ep of the eye E or the position of the bright spot image (corneal vertex Ea) formed by the XY alignment index projection optical system 22 in the image (its data). If this is the case, the amount of deviation (size and direction) between these positions and the current position of the optical axis O1 of the intraocular pressure measuring unit 20 can be recognized. A reference position in S12 is determined.

  In step S12, following the execution of automatic alignment for the eye ER of the eye pressure measurement unit 20 (second measurement unit) in step S11, the intraocular pressure measurement unit 20 (second measurement unit) uses the binocular interval dm. The left / right switching movement for both eyes E is performed, and the process proceeds to step S13. In step S12, since the intraocular pressure of the eye ER to be examined has been measured and the intraocular pressure of the eye EL to be examined has not yet been measured, the apparatus body 13 is placed on the eye EL side (X axis direction positive side). , To perform general alignment with respect to the eye ER to be examined. Specifically, in step S12, the apparatus main body 13 is first retracted (moved to the negative side in the Z-axis direction), and the airflow spray nozzle 21b of the intraocular pressure measurement unit 20 is moved away from the eye ER to be examined. In the present embodiment, the apparatus main body 13 is retracted to the end in the movable range in the Z-axis direction. Thereafter, in step S12, the eye distance EL measured by the binocular interval dm calculated and stored in step S6 is moved toward the eye to be examined (basically on the positive side in the X-axis direction and may be moved in the Y-axis direction or the Z-axis direction in some cases). Move. This completes the left-right switching movement of the eye E (in this example, the eye EL from the eye ER to be examined). That is, in step S12, the apparatus main body unit 13, that is, the intraocular pressure measurement unit 20, is substantially connected to the position where the intraocular pressure measurement unit 20 is appropriate for the eye ER to be examined by the automatic alignment in step S11. The eye distance dm is moved toward the eye EL to be examined. In step S11, the pupil in the image (data) of the anterior segment (cornea Ec) acquired by the anterior segment observation optical system 21 (second observation optical system) of the tonometry unit 20 (second measurement unit). When moving to a position where the center position of Ep or the position of the bright spot image (corneal vertex Ea) can be detected, as described above, the shift amount is used as a correction value, and the distance between both eyes dm. Determine the reference position to move.

  In step S13, following the left-right switching movement of the intraocular pressure measurement unit 20 (second measurement unit) using the binocular interval dm in step S12 with respect to both eyes E, the intraocular pressure measurement unit 20 (second measurement unit) Automatic alignment is performed on the eye EL to be examined, and the process proceeds to step S14. In step S13, as in step S9, automatic alignment is performed on the eye EL to be examined. Then, the apparatus main body 13 is moved to the positive side in the Z-axis direction, the intraocular pressure measurement unit 20 approaches the eye to be examined EL, and the tip of the airflow nozzle 21b is moved from the eye EL to the second set working distance d2. It is supposed to be located in As a result, the eye EL to be examined is positioned on the optical axis O1 of the tonometry part 20, and the tip of the tonometry part 20 is located at the second set working distance d2 from the eye EL. The pressure measuring unit 20 is set to a position suitable for the eye to be examined EL.

  In step S14, following the execution of automatic alignment of the eye pressure measurement unit 20 (second measurement unit) with respect to the subject eye EL in step S13, the intraocular pressure of the eye EL to be examined by the tonometry unit 20 (second measurement unit) is measured. The measurement is performed and the left and right eye switching operation processing (left and right eye switching operation method) is completed. In step S14, as described above, the intraocular pressure of the eye to be examined EL is measured by the intraocular pressure measurement unit 20.

  Next, using the ophthalmologic apparatus 10, the eye characteristics of both eyes E are measured by the eye characteristics measuring section 40 (first measuring section), and both eyes E are measured by the intraocular pressure measuring section 20 (second measuring section). The operation related to the left / right eye switching operation method when measuring the intraocular pressure of the eye will be described.

  First, when an operation for starting measurement by the eye characteristic measurement unit 40 (first measurement unit) is performed, automatic alignment is performed on the eye EL to be examined by proceeding from step S1 to step S2 in the flowchart of FIG. After that, the eye characteristic of the eye to be examined EL is measured by the eye characteristic measurement unit 40 (first measurement unit) (see FIG. 7A). Thereafter, in the flowchart of FIG. 9, by proceeding from step S3 → step S4 → step S5 → step S6, the eye characteristic measurement unit 40 (first measurement unit) that is set to a position suitable for the eye to be examined in step S3 From the eye characteristic measurement unit 40 (first measurement unit) that has been positioned to match the eye ER in step S5, the binocular interval dm between both eyes E (the eye EL to be examined and the eye ER to be examined) is calculated. And remember. Thereafter, in the flowchart of FIG. 9, by proceeding from step S7 to step S8, the eye characteristic measurement unit 40 (first measurement unit) positioned at a position suitable for the eye ER to be measured measures the eye characteristic of the eye ER to be examined. (See FIG. 7B), and the mode is switched to the intraocular pressure measurement mode (see FIGS. 5B to 5A).

  In the flowchart of FIG. 9, by proceeding from step S <b> 9 to step S <b> 10, the intraocular pressure measurement of the eye ER to be examined by the intraocular pressure measurement unit 20 (second measurement unit) is performed after performing automatic alignment on the eye ER to be examined. Is performed (see FIG. 10A). Then, in the flowchart of FIG. 9, by proceeding to step S11, automatic alignment is performed and the intraocular pressure measurement unit 20 (second measurement unit) is set to a position that matches the eye ER to be examined (FIG. 10A). reference). Then, in the flowchart of FIG. 9, by proceeding to step S12, the intraocular pressure measurement unit 20 (the first intraocular pressure measurement unit 20) is used with reference to the position (the intraocular pressure measurement unit 20) that matches the eye ER to be examined by the automatic alignment in step S11. 2 measuring unit) is moved toward the eye EL to be examined by the distance dm between both eyes (see (a) to (c) of FIG. 10). Thereafter, in the flowchart of FIG. 9, by proceeding from step S13 to step S14, the intraocular pressure of the eye EL is measured by the intraocular pressure measurement unit 20 (second measurement unit) after performing automatic alignment on the eye EL to be examined. This is performed (see FIG. 10D).

  As described above, in the ophthalmologic apparatus 10, basically, both eyes of both eyes E obtained when measuring the left and right eye E of the subject using the eye characteristic measuring unit 40 (first measuring unit). Using the interval dm, the left and right eye E are switched during measurement by the intraocular pressure measurement unit 20 (second measurement unit). This is because the following problems occur when the left-right switching movement with respect to the eye E is performed by detecting the pupil Ep using the intraocular pressure measurement unit 20. Below, this problem is demonstrated using FIG. 10 and FIG. Note that this problem may occur in the ophthalmologic apparatus 10 and will be described using the ophthalmologic apparatus 10.

  In the intraocular pressure measurement unit 20 as the second measurement unit, the second set working distance d2 is set to a very small value as described above. For this reason, the intraocular pressure measurement unit 20 measures one eye E (for example, the eye ER to be examined) (see FIG. 10A), and then once the second set working distance from the subject (each eye E). It is necessary to move in the X-axis direction (see FIGS. 10B and 10C) after being far away from d2. This is because when the intraocular pressure measurement unit 20 moves in the X-axis direction while maintaining the second set working distance d2, the tip (airflow spray nozzle 21b) interferes with the subject (mainly the nose). Because it ends up.

  In the intraocular pressure measurement unit 20, an image of the anterior segment is acquired by the CCD camera 21 i of the anterior segment observation optical system 21, and the image (its data) is output to the control unit 33. For this reason, the intraocular pressure measurement unit 20 can detect the position of the pupil Ep in the eye E (cornea Ec) in the input image (its data), similarly to the eye characteristic measurement unit 40. Yes. However, in the intraocular pressure measurement unit 20, the second set working distance d2 is set to a very small value, and is larger than the second set working distance d2 when moved in the X-axis direction as described above. Being separated. Further, since the anterior ocular segment observation optical system 21 is provided for measurement by the intraocular pressure measurement unit 20, the object to be measured that is set as the second set working distance d2 of the intraocular pressure measurement unit 20 is concerned. The optometry E is properly focused. For this reason, in the intraocular pressure measurement part 20 (control part 33), the image of the anterior eye part (pupil Ep) will become blurred, and it will become difficult to detect the pupil Ep appropriately.

  In the intraocular pressure measurement unit 20 (ophthalmologic apparatus 10) of the present embodiment, the position on the optical axis O1 of the CCD camera 21i is set as the second focal position f2 (see FIG. 3) via the focusing drive mechanism 21D. Thus, an image of the eye E (the anterior eye portion (cornea Ec)) can be appropriately displayed on the display unit 14. For this reason, in the ophthalmologic apparatus 10 (intraocular pressure measurement unit 20), the problem due to the in-focus state is basically solved.

  Further, in the intraocular pressure measurement unit 20, the anterior ocular segment observation optical system 21 passes outside the airflow spray nozzle 21b, passes through the anterior ocular window glass 21c (including a glass plate 34b described later), the chamber window glass 21d, and the half mirror. 21g and the half mirror 21e are transmitted, converged by the objective lens 21f, and formed on the CCD camera 21i (its light receiving surface), thereby obtaining an anterior segment image (its luminous flux) of the eye E to be examined. (Refer to FIG. 3 etc.). For this reason, in the image (on the screen of the display unit 14) acquired by the anterior ocular segment observation optical system 21, as shown in FIG. It will be. The out-of-focus airflow spray nozzle 21b (its shadow) may be erroneously detected as the pupil Ep. This is because the pupil Ep and the airflow spray nozzle 21b (its shadow) are similar to each other in the image (on the screen of the display unit 14) when the pupil Ep is detected in an out-of-focus state. Since it can be an image, there is a possibility that the possibility increases.

  This erroneous detection of the pupil Ep may increase the time required for automatic rough alignment or may cause rough alignment. For these reasons, in the intraocular pressure measurement unit 20 (second measurement unit) in which the second set working distance d2 is set to a very small value, from the position suitable for one eye E (for example, eye E), the other It is desirable to increase the accuracy of performing automatic rough alignment when automatically moving to a position suitable for the eye E.

  On the other hand, in the ophthalmologic apparatus 10 as an embodiment of the ophthalmologic apparatus according to the present invention, when the left and right eye E of the subject is measured using the eye characteristic measurement unit 40 (first measurement unit). The binocular interval dm of both eyes E is obtained, and the left and right eye E are switched during the measurement by the intraocular pressure measurement unit 20 (second measurement unit) using the obtained binocular interval dm. Therefore, in the ophthalmologic apparatus 10, the binocular interval dm is set without using the second observation optical system (anterior ocular segment observation optical system 21) of the intraocular pressure measurement unit 20 (second measurement unit) that can erroneously detect the pupil Ep. Since the intraocular pressure measurement unit 20 (second measurement unit) is moved to the other eye E side using the eye, the eye is surely opposed to the other eye E (pupil Ep) without getting lost. The pressure measurement unit 20 (second measurement unit) can be moved. Thereby, in the ophthalmologic apparatus 10, the intraocular pressure measurement part 20 (2nd measurement part) can be automatically moved appropriately to the position suitable for the other eye E to be examined.

  Further, in the ophthalmologic apparatus 10, the anterior ocular segment observation optical of the intraocular pressure measurement unit 20 (second measurement unit) is switched when the right and left eye E is switched in the measurement by the intraocular pressure measurement unit 20 (second measurement unit). Since the pupil Ep detected by the system 21 is not used, it is possible to prevent the pupil Ep from being affected by erroneous detection of the pupil Ep in the anterior ocular segment observation optical system 21.

  Further, in the ophthalmologic apparatus 10, the intraocular pressure measurement unit 20 (second measurement unit) can be reliably moved to a position facing the other eye E (pupil Ep) without getting lost. Alignment of the intraocular pressure measurement unit 20 (second measurement unit) with respect to the subject eye E can be performed appropriately and quickly. For this reason, in the ophthalmologic apparatus 10, the intraocular pressure measurement unit 20 (second measurement unit) can be automatically and appropriately moved to a position suitable for the other eye E.

  The ophthalmologic apparatus 10 does not use the pupil Ep detected by the anterior ocular segment observation optical system 21 of the intraocular pressure measurement unit 20 (second measurement unit), so that the combination provided in the tonometry unit 20 (ophthalmology apparatus 10) is not used. Even if the position on the optical axis O1 of the CCD camera 21i is not set to the second focal position f2 via the focus drive mechanism 21D, the intraocular pressure measurement unit 20 (second measurement unit) is adapted to the other eye E to be examined. It can be moved automatically and appropriately. For this reason, in the ophthalmologic apparatus 10, the focus drive mechanism 21D of the intraocular pressure measurement unit 20 (the ophthalmologic apparatus 10) can be eliminated. For this reason, even in an ophthalmologic apparatus not provided with a mechanism corresponding to the focusing drive mechanism 21D, the intraocular pressure measurement unit 20 (second measurement unit) is automatically moved to a position suitable for the other eye E. Can be moved appropriately.

  In the ophthalmologic apparatus 10, after one eye E is measured using the intraocular pressure measurement unit 20 (second measurement unit), the intraocular pressure measurement unit 20 (second measurement unit) is aligned with respect to the one eye E. After that, the intraocular pressure measurement unit 20 (second measurement unit) is moved to the other eye E side by the previously obtained binocular interval dm. For this reason, even if the subject moves his / her face after measuring one eye E using the intraocular pressure measuring unit 20 (second measuring unit), Since the intraocular pressure measurement unit 20 (second measurement unit) is moved by a distance dm between both eyes with reference to the position of the subject eye E, the intraocular pressure measurement unit is automatically and more appropriately moved to a position facing the other eye E. 20 (second measurement unit) can be moved.

  In the ophthalmologic apparatus 10, since the second measurement unit is the intraocular pressure measurement unit 20, after measuring one eye E using the intraocular pressure measurement unit 20 (second measurement unit) as described above, It is possible to make the alignment of the intraocular pressure measurement unit 20 (second measurement unit) with respect to the eye E more effective. This is because the intraocular pressure measuring unit 20 measures the intraocular pressure by spraying a fluid on the cornea Ec of the eye E to deform the cornea Ec. This is because there are many scenes where people move their faces by feeling uncomfortable.

  In the ophthalmologic apparatus 10, the position of the eye characteristic measurement unit 40 (first measurement unit) that has performed alignment on one eye E and the eye characteristic measurement unit 40 (on which alignment has been performed on the other eye E). The binocular distance dm is obtained based on the position of the first measurement unit. For this reason, the ophthalmologic apparatus 10 can obtain the binocular distance dm more appropriately.

  In the ophthalmologic apparatus 10, an eye characteristic measuring unit 40 (first measuring unit) that performs alignment on one eye E after measuring one eye E using the eye characteristic measuring unit 40 (first measuring unit). ) And the position of the eye characteristic measurement unit 40 (first measurement unit) that has been aligned with respect to the other eye E thereafter, the binocular interval dm is obtained. For this reason, in the ophthalmologic apparatus 10, even if the subject moves his / her face after measuring one eye E using the eye characteristic measurement unit 40 (first measurement unit), the movement Since the binocular distance dm can be obtained with reference to the position of one eye E to be examined in the face, the binocular distance dm can be obtained more appropriately.

  In the ophthalmologic apparatus 10, after one eye E is measured using the eye characteristic measurement unit 40 (first measurement unit), the anterior eye acquired by the observation optical system 42 of the eye characteristic measurement unit 40 (first measurement unit). The eye characteristic measurement unit 40 (first measurement unit) is moved to the other eye E side with the position of the pupil Ep detected based on the image of the part as a target. Here, since the eye characteristic measurement unit 40 (first measurement unit) is set to a relatively large first set working distance d1, the other subject is not retracted when the left and right eye E is switched. Since it can be moved to the optometry E side, no erroneous detection of the pupil Ep basically occurs. Therefore, in the ophthalmologic apparatus 10, the eye characteristic measurement unit 40 (first measurement unit) can obtain the binocular interval dm with high accuracy, and the intraocular pressure measurement unit 20 (second measurement) using the binocular interval dm. Part) to the other eye E side, the intraocular pressure measurement part 20 (second measurement part) can be automatically and appropriately moved to a position facing the other eye E.

  In the ophthalmologic apparatus 10, when the control unit 33 measures the position of the eye characteristic measurement unit 40 (first measurement unit) in the XYZ directions when measuring one eye E and the other eye E. The position of the eye characteristic measuring unit 40 (first measuring unit) in each of the XYZ directions is stored. In the ophthalmologic apparatus 10, the control unit 33 obtains the binocular interval dm that is the interval between the left and right eye E by obtaining the difference in position in both directions of both XYZ, and the obtained binocular interval dm. Remember. For this reason, in the ophthalmologic apparatus 10, the amount of movement of each of the Y-axis drive portion 12a, the Z-axis drive portion 12b, and the X-axis drive portion 12c in the drive unit 12 (control amount for the movement (in this embodiment, the number of pulses) )) Can be used to move the intraocular pressure measurement unit 20 (second measurement unit). Thereby, in the ophthalmologic apparatus 10, the magnitude | size and direction (binocular space | interval dm) which moved the eye characteristic measurement part 40 (1st measurement part) by the drive part 12 are completely the same magnitude | size and direction (binocular space | interval dm). ) To move the intraocular pressure measurement unit 20 (second measurement unit). Therefore, in the ophthalmologic apparatus 10, the intraocular pressure measurement unit 20 (second measurement unit) is automatically moved to a position more appropriately facing the other eye E while simplifying control for movement. Can do.

  In the ophthalmologic apparatus 10, the binocular interval dm is obtained using the corneal vertex Ea (the position) of the cornea Ec of both eyes E. For this reason, the ophthalmologic apparatus 10 measures the intraocular pressure of the eye E, and measures the intraocular pressure by making the optical axis O1 coincide with the corneal vertex Ea (the position) of the cornea Ec of the eye E. According to the aspect of the unit 20 (second measurement unit), it can be appropriately matched, and the intraocular pressure measurement unit 20 (second measurement unit) is automatically moved to a position more appropriately facing the other eye E. Can do.

  In the ophthalmologic apparatus 10, the position of the eye characteristic measurement unit 40 (first measurement unit) that has performed alignment on one eye E and the eye characteristic measurement unit 40 (on which alignment has been performed on the other eye E). Since the binocular interval dm is obtained based on the position of the first measuring unit), the binocular interval dm is obtained from the corneal apex Ea of both eyes E using the position of the apparatus main body unit 13. For this reason, in the ophthalmologic apparatus 10, it is possible to more easily match with the mode of the intraocular pressure measurement unit 20 (second measurement unit) more easily, and the intraocular pressure measurement unit 20 (second measurement unit) can be matched with the other eye E. And can be moved automatically to a more appropriate facing position.

  The ophthalmologic apparatus 10 uses the image (its data) of the anterior segment (cornea Ec) acquired by the observation optical system 42 (first observation optical system) of the eye characteristic measurement unit 40 (first measurement unit). dm can be determined. For this reason, in the ophthalmologic apparatus 10, it is possible to obtain an appropriate binocular interval dm without accurately aligning the eye characteristic measurement unit 40 (first measurement unit) with the eye E. Thereby, in the ophthalmologic apparatus 10, the intraocular pressure measurement part 20 (2nd measurement part) can be automatically moved to the position which opposes the other eye E more appropriately more easily.

  In the ophthalmologic apparatus 10, the center position of the pupil Ep in the image (its data) of the anterior segment (cornea Ec) acquired by the observation optical system 42 (first observation optical system) of the eye characteristic measurement unit 40 (first measurement unit). Can be used to obtain the binocular distance dm. For this reason, in the ophthalmologic apparatus 10, even when the alignment is not performed so that the optical axis coincides with the corneal apex Ea, the intraocular pressure measurement unit 20 (second measurement unit) is connected to the other eye E to be examined. It can be automatically moved to an appropriately facing position. This is because, for example, when the eye refractive power is measured by the eye characteristic measurement unit 40 (first measurement unit), alignment may be performed so that the optical axis coincides with the center position of the pupil Ep, This is because when the optometry E is a cataract eye and the lens is clouded, alignment may be performed while avoiding the cloud. In such a case, in the image (its data) of the anterior segment (cornea Ec) acquired by the observation optical system 42 (first observation optical system) of the eye characteristic measurement unit 40 (first measurement unit), The amount of deviation (size and direction) between the center position of the pupil Ep and the corneal apex Ea is detected, and the intraocular pressure measurement unit 20 (second measurement unit) is moved using the binocular interval dm. It is desirable to make corrections.

  In the ophthalmologic apparatus 10, the magnification of the anterior ocular segment observation optical system 21 (second observation optical system) in the intraocular pressure measurement unit 20 (second measurement unit) is set as the observation optical system in the eye characteristic measurement unit 40 (first measurement unit). It can be set higher than the magnification of 42 (first observation optical system). Then, in the ophthalmologic apparatus 10, since the accuracy of alignment in the tonometry part 20 (second measurement part) can be increased, the measurement result of the intraocular pressure of the eye E to be examined by the tonometry part 20 (second measurement part). However, it can be prevented from being affected by a decrease in alignment accuracy. That is, in the ophthalmologic apparatus 10, an appropriate measurement result of the intraocular pressure of the eye E can be obtained more reliably by the intraocular pressure measurement unit 20 (second measurement unit). However, if the setting is as described above, the anterior ocular segment observation optical system 21 (second observation optical system) of the intraocular pressure measurement unit 20 (second measurement unit) detects the pupil Ep because the imaging range becomes narrow. In addition to difficulty, the focal depth becomes shallower and the focus is likely to be blurred. For this reason, in the ophthalmologic apparatus 10, it becomes more difficult to detect the pupil Ep by the anterior ocular segment observation optical system 21 (second observation optical system) of the intraocular pressure measurement unit 20 (second measurement unit). Therefore, in the ophthalmologic apparatus 10, when the above setting is made, both eyes are used without using the anterior ocular segment observation optical system 21 (second observation optical system) of the intraocular pressure measurement unit 20 (second measurement unit). It can be made more effective to move the intraocular pressure measurement unit 20 (second measurement unit) to the other eye E side using the interval dm.

  Therefore, in the ophthalmologic apparatus 10 as an embodiment of the ophthalmologic apparatus according to the present invention, the intraocular pressure measuring unit 20 (second measuring unit) set to the second set working distance d2 having a value smaller than the first set working distance d1. ) Can be automatically and appropriately moved from a position suitable for one eye E to a position suitable for the other eye E.

  In the above-described embodiment, the ophthalmologic apparatus 10 as an embodiment of the ophthalmologic apparatus according to the present invention has been described, but the first set at the first set working distance in order to measure the subject's eye to be examined. A measurement unit; a second measurement unit set to a second set working distance shorter than the first set working distance to measure the eye to be examined; the first measuring unit and the first to the eye to be examined 2 a drive unit that moves the measurement unit, and a control unit that controls the first measurement unit, the second measurement unit, and the drive unit, the control unit using the first measurement unit When the first measurement unit is moved to measure the left and right eyes of the subject, the distance between the left and right eyes is obtained, and one eye is examined using the second measurement unit. After the measurement, the second measuring unit is moved to the other eye side by the determined distance between the eyes. Cause may be an ophthalmic device, but is not limited to the aforementioned embodiments.

  In the above-described embodiment, after one eye E is measured using the intraocular pressure measurement unit 20 (second measurement unit), the intraocular pressure measurement unit 20 (second measurement unit) for one eye E is measured. After the alignment, the intraocular pressure measurement unit 20 (second measurement unit) is moved to the other eye E side by the calculated distance between eyes dm. However, when one eye E is measured using the intraocular pressure measurement unit 20 (second measurement unit), the intraocular pressure measurement unit 20 (first eye) is measured toward the other eye E side by the distance between both eyes dm obtained from the position. 2 measuring unit) may be moved, and is not limited to the above-described embodiment. This is because when the one eye E is measured using the intraocular pressure measurement unit 20 (second measurement unit), the alignment of the tonometry unit 20 (second measurement unit) with respect to the one eye E is determined. By being completed.

  Further, in the above-described embodiment, the eye characteristic measuring unit 40 (first measurement unit) (first measurement unit) is used to measure one eye E and then align the eye E with the eye characteristic measuring unit 40 (first measurement). The binocular interval dm is obtained based on the position of the first measuring unit) and the position of the eye characteristic measuring unit 40 (first measuring unit) that has been aligned with respect to the other eye E thereafter. However, the eye characteristic measurement unit 40 (first measurement) that is aligned with respect to the position where one eye E is measured using the eye characteristic measurement unit 40 (first measurement unit) and then the other eye E is measured. The distance between both eyes dm may be obtained based on the position of the (part), and is not limited to the above-described embodiment. This is because, when one eye E is measured using the eye characteristic measurement unit 40 (first measurement unit), the alignment of the eye characteristic measurement unit 40 (first measurement unit) with respect to the one eye E to be examined is aligned. By being completed.

  In the above-described embodiment, the intraocular pressure measurement unit 20 is mounted as the second measurement unit. However, if the second setting working distance d2 is set to a value smaller than the first setting working distance d1, the optical pressure measurement unit 20 is optical. It may be an intraocular pressure measuring unit having a different configuration, arrangement of optical members, and measurement principle, or may be a pachymeter that measures the thickness of the cornea (corneal thickness measurement), and is limited to the above-described embodiments. is not.

  In the above-described embodiment, the eye characteristic measurement unit 40 (first measurement unit) targets the position of the pupil Ep detected based on the image of the anterior segment acquired by the observation optical system 42 as the target eye E side. The eye characteristic measurement unit 40 (first measurement unit) is moved to the side. However, after measuring one eye E using the eye characteristic measurement unit 40 (first measurement unit), the eye characteristic measurement unit 40 (first measurement unit) is automatically moved to a position facing the other eye E. As long as it moves, it is not limited to the above-described embodiment.

  In the above-described embodiment, the eye characteristic measurement unit 40 is mounted as the first measurement unit. However, if the reflected light from the eye E is received and the optical characteristic of the eye E is measured, the optical characteristic is measured. The configuration, the arrangement of each optical member, and the measurement principle may be different, the content (type) of measurement may be different, and the present invention is not limited to the above-described embodiments.

  In the above-described embodiment, the position of the CCD camera 21i is switched between the first focal position f1 and the second focal position f2 in the intraocular pressure measurement unit 20, but the front of the eye E to be examined is moved by moving the CCD camera 21i. As long as the eye (the cornea Ec) is focused, the movement mode may be set as appropriate, and is not limited to the above-described embodiment.

  In the above-described embodiment, the eye characteristic measurement unit 40 as the first measurement unit is integrally provided below the intraocular pressure measurement unit 20 as the second measurement unit. However, the first measurement unit and the second measurement unit are provided. The first measurement unit and the second measurement unit may be individually movable by the drive unit, and are not limited to the above-described embodiments.

  As described above, the ophthalmologic apparatus of the present invention has been described based on the embodiments. However, the specific configuration is not limited to the embodiments, and design changes and additions are allowed without departing from the gist of the present invention. The

DESCRIPTION OF SYMBOLS 10 Ophthalmologic apparatus 12 Drive part 20 Intraocular pressure measurement part (As an example of a measurement part) 33 Control part 40 Eye characteristic measurement part (As an example of a measurement part) E Eye to be examined dm Binocular interval

Claims (3)

A measuring unit for measuring the subject's eye;
A drive unit for moving the measurement unit with respect to the eye to be examined;
A control unit for controlling the measurement unit and the drive unit,
The control unit measures the one eye to be examined by the measuring unit after performing alignment of the measuring unit with respect to the one eye to be examined, and performs the measurement on one eye to be examined after measurement of the one eye to be examined. The ophthalmologic apparatus is characterized in that the position of the measurement unit in a state where the alignment is completed and the alignment is completed is stored.   2. The control unit according to claim 1, wherein the control unit moves the measurement unit to the other eye side after storing the position of the measurement unit in a state where alignment after measurement is completed. Ophthalmic equipment. The control unit performs alignment of the measurement unit with respect to the other eye to be examined after moving the measurement unit, and stores the position of the measurement unit that has performed alignment with respect to the stored one eye to be examined, and after the movement The ophthalmologic apparatus according to claim 2, wherein a binocular interval of the eye to be examined is obtained based on the position of the measurement unit that has aligned the other eye to be examined.