JP7265903B2 - ophthalmic equipment - Google Patents

Description

The present disclosure relates to ophthalmic devices.

Misalignment of the eyes is known to cause poor visual performance, eyestrain, etc., and is sometimes corrected with a prism lens or the like. Therefore, an ophthalmologic apparatus capable of determining the eye position has been proposed (see Patent Document 1).

This ophthalmologic apparatus has a wavelength selection characteristic that blocks visible light and transmits non-visible light for measurement. It is possible to forcibly switch the vision and obtain the degree of obliqueness of the occluded eye, and to measure accommodation when no visible light is incident on the eye.

Japanese Patent No. 5011144

However, the above-described ophthalmologic apparatus acquires the degree of obliqueness of the closed eye by forcibly switching between binocular vision and monocular vision. Here, it is desirable to measure the relationship between convergence and accommodation in the state of binocular vision in order to accurately determine the cause of poor visual performance, eye strain, and the like. Therefore, the ophthalmologic apparatus described above has room for improvement from the viewpoint of appropriately measuring the relationship between convergence and accommodation.

The present disclosure has been made in view of the above circumstances, and aims to provide an ophthalmologic apparatus capable of appropriately measuring the relationship between convergence and accommodation.

In order to solve the above-described problems, an ophthalmologic apparatus according to the present disclosure is provided in pairs corresponding to both eyes to be examined of a subject, and provides an eye information acquisition apparatus that presents a fixation image to at least the eyes to be examined. a drive mechanism that adjusts the positions of the two eye information acquisition units and rotates them around the corresponding eyeball rotation point of the eye to be examined; and a control unit that controls the eye information acquisition unit and the drive mechanism. and the control unit changes the focal distance of the fixation image in the eye information acquisition unit and the rotation angle of the eye information acquisition unit while presenting the fixation image, thereby It is characterized by obtaining the relationship between convergence and accommodation in optometry.

According to the ophthalmologic apparatus of the present disclosure, it is possible to appropriately measure the relationship between convergence and accommodation.

1 is an explanatory diagram showing the overall configuration of an ophthalmologic apparatus according to a first embodiment as an example of an ophthalmologic apparatus according to the present disclosure; FIG. FIG. 4 is an explanatory view schematically showing a configuration in which a pair of measuring heads are movable via a drive mechanism in an ophthalmologic apparatus; FIG. 3 is an explanatory diagram showing a schematic configuration of an eye information acquisition unit of an ophthalmologic apparatus; 3 is a block diagram showing the configuration of the control system of the ophthalmologic apparatus; FIG. FIG. 4 is an explanatory diagram showing the configuration of an optical system of an eye information acquisition unit; FIG. 10 is an explanatory diagram showing the relationship between the presentation position, the focusing distance, and the rotation angle; FIG. 4 is an explanatory diagram showing a fixation image presented to the left eye to be examined and a fixation image presented to the right eye to be examined side by side, as an example of a fixation image that does not stimulate fusion. In the case of using a fixation image as an example that does not stimulate fusion, the left and right fixation images are properly binocularly viewed above, and the left and right fixation images are not properly binocularly viewed. It is explanatory drawing shown below. FIG. 4 is an explanatory diagram showing a fixation image presented to the left eye to be examined and a fixation image presented to the right eye to be examined, arranged side by side, as an example of a fixation image that stimulates fusion. FIG. 10 is an explanatory diagram showing a state in which left and right fixation images are fused in a case where a fixation image is used as an example of stimulating fusion. FIG. 10 is an explanatory diagram showing how the presentation position is changed from the reference plane to the displacement plane to obtain the adjustment amount; 4 is a flowchart showing measurement control processing (measurement control method) executed by the control unit of the ophthalmologic apparatus;

Example 1 of an ophthalmic device 10 as one embodiment of the ophthalmic device according to the present disclosure will be described below with reference to FIGS. 1 to 12 . 5, 6 and 11 omit the deflecting member 26 in order to facilitate understanding of the configuration and contents shown therein. 6 and 11 show the vertical scale of the presentation position Pp and the interpupillary distance when viewed from the front in order to facilitate understanding of the relationship between the presentation position, the focal distance, and the rotation angle. The scale in the horizontal direction showing the PD is different.

As shown in FIG. 1, the ophthalmologic apparatus 10 includes a base 11 installed on the floor, an optometry table 12, a column 13, an arm 14 as a support, a drive mechanism 15, and a pair of measurement heads. 16 and. The ophthalmologic apparatus 10 is configured such that the subject facing the eye examination table 12 presses the forehead against the forehead support 17 provided between the measuring heads 16, and the subject's eye to be examined E (see FIG. 3). etc.). Hereinafter, when viewed from the subject, the left-right direction is the X direction, the up-down direction (vertical direction) is the Y direction, and the direction orthogonal to the X and Y directions (the depth direction of the measurement head 16 (the subject side is The front side)) is the Z direction.

The optometry table 12 is a desk on which an examiner controller 31 and a subject controller 32 (see FIG. 4), which will be described later, are placed, and objects used for optometry are placed, and is supported by the base 11 . . The optometric table 12 may be supported by the base 11 so that its position in the Y direction (height position) can be adjusted.

The post 13 is erected in the Y direction from the rear end of the optometry table 12, and an arm 14 is provided on the top. The arm 14 suspends a pair of measuring heads 16 on the optometry table 12 via a drive mechanism 15, and extends in the Z direction from the column 13 toward the near side. The arm 14 is movable in the Y direction with respect to the column 13, and its position (height position) in the Y direction is adjusted by an arm driving mechanism 34 (see FIG. 4), which will be described later. In addition, the arm 14 may be movable in the X direction and the Z direction with respect to the column 13 . Both measuring heads 16 are suspended from the tip of the arm 14 by a drive mechanism 15 and supported.

The measuring heads 16 are provided in pairs so as to individually correspond to the left and right eyes E of the subject to be examined. is a left eye measurement head 16L, and the one that acquires information on the subject's right eye E to be examined is a right eye measurement head 16R. The left-eye measurement head 16L and the right-eye measurement head 16R are configured to be symmetrical with respect to a vertical plane positioned between them in the X direction.

Each measuring head 16 includes an eye information acquisition unit 21 (referred to as a right eye information acquisition unit 21R and a left eye information acquisition unit 21L (see FIG. 2) when describing separately) for acquiring eye information of the eye E to be examined. Contained. The eye information necessarily includes the refractive power of the eye E to be examined, and also includes an image of the eye E to be examined, an image of the fundus Ef of the eye E to be examined (see FIG. 5), and a retina of the eye E to be examined. , the corneal endothelium image of the eye to be examined E, the corneal shape of the eye to be examined E, the intraocular pressure of the eye to be examined E, and the like are appropriately combined. Each eye information acquisition unit 21 necessarily includes a target presenting mechanism for presenting a target. Each eye information acquisition unit 21 also includes a refractive power measuring mechanism (a refractometer in Example 1) for measuring refractive power, a vision test device for performing a vision test while switching the visual target to be presented, and a corrective lens. A phoropter that acquires the correct refractive power of the subject's eye E by switching it, a wavefront sensor that measures the refractive power, a fundus camera that captures an image of the fundus, a tomography device (OCT (Optical Coherence Tomography)), a specular microscope for taking an image of the corneal endothelium, a keratometer for measuring corneal shape, a tonometer for measuring intraocular pressure, etc. are appropriately combined.

Both measuring heads 16 are movably suspended by a drive mechanism 15 via a mounting base portion 18 provided at the tip of the arm 14, as shown in FIG. In the first embodiment, the drive mechanism 15 includes a left vertical drive section 22L, a left horizontal drive section 23L, a left Y-axis rotation drive section 24L, a left X-axis rotation drive section 25L, and a right eye measurement head 16L. It has a right vertical drive section 22R, a right horizontal drive section 23R, a right Y-axis rotation drive section 24R, and a right X-axis rotation drive section 25R corresponding to the measurement head 16R. The configuration of each drive unit corresponding to the left eye measurement head 16L and the configuration of each drive unit corresponding to the right eye measurement head 16R are plane symmetrical with respect to a vertical plane positioned between them in the X direction. They are simply referred to as a vertical drive section 22, a horizontal drive section 23, a Y-axis rotation drive section 24, and an X-axis rotation drive section 25, unless otherwise specified. The drive mechanism 15 is provided with a vertical drive section 22, a horizontal drive section 23, a Y-axis rotation drive section 24, and an X-axis rotation drive section 25 in this order from the arm 14 side.

The mounting base part 18 is fixed to the tip of the arm 14 and extends in the X direction. Each driving part (22R, 23R, 24R, 25R) is suspended. A forehead support portion 17 is provided in the central portion of the mounting base portion 18 .

The vertical driving portion 22 is provided between the mounting base portion 18 and the horizontal driving portion 23 and moves the horizontal driving portion 23 in the Y direction (vertical direction) with respect to the mounting base portion 18 . The horizontal drive unit 23 is provided between the vertical drive unit 22 and the Y-axis rotation drive unit 24, and moves the Y-axis rotation drive unit 24 in the X direction and the Z direction (horizontal direction) with respect to the vertical drive unit 22. . The vertical drive unit 22 and the horizontal drive unit 23 include an actuator such as a pulse motor that generates a driving force, and a transmission mechanism that transmits the driving force such as a combination of gears or a rack and pinion. set up and configured. The horizontal drive unit 23 can be easily configured and easily controlled for movement in the horizontal direction by providing separate combinations of actuators and transmission mechanisms for the X and Z directions, for example.

The Y-axis rotation drive unit 24 is provided between the horizontal drive unit 23 and the X-axis rotation drive unit 25, and the X-axis rotation drive unit 25 is connected to the horizontal drive unit 23 at the corresponding eyeball rotation point of the eye E to be examined. , which extends in the Y direction through the Y axis of eye rotation. The X-axis rotation drive section 25 is provided between the Y-axis rotation drive section 24 and the corresponding measurement head 16, and rotates the corresponding measurement head 16 with respect to the Y-axis rotation drive section 24 to the eyeball of the eye E to be examined. Rotate around the X-axis of eyeball rotation passing through the rotation point and extending in the X-direction. The Y-axis rotation driving section 24 and the X-axis rotation driving section 25, for example, have an actuator and a transmission mechanism like the vertical driving section 22 and the horizontal driving section 23, and the transmission mechanism receives the driving force from the actuator. moves along an arcuate guide groove. The Y-axis rotation drive unit 24 can rotate the measurement head 16 around the eyeball rotation Y-axis of the eye E to be examined by aligning the center position of the guide groove with the eyeball rotation Y-axis. Further, the X-axis rotation drive unit 25 can rotate the measurement head 16 about the X-axis of eyeball rotation of the eye E to be examined by aligning the center position of the guide groove with the X-axis of eyeball rotation. Therefore, the measuring head 16 is arranged so that the center position of each of the guide grooves of the Y-axis rotation drive unit 24 and the X-axis rotation drive unit 25 coincides with the eyeball rotation point of the eye E to be examined. , in the left-right direction (rotating direction about the Y direction) and the vertical direction (rotating direction about the X direction).

The Y-axis rotation driving section 24 supports the measuring head 16 so as to be rotatable around its own Y-axis rotation axis, and cooperates with the horizontal driving section 23 to rotate the measuring head through the X-axis rotation driving section 25 . The measurement head 16 may be rotated around the eyeball rotation Y axis of the eye E to be inspected by rotating while changing the supporting position of the measurement head 16 . In addition, the X-axis rotation driving section 25 supports the measuring head 16 so as to be rotatable around the X-axis rotation axis provided therein, and cooperates with the vertical driving section 22 to change the position at which the measuring head 16 is supported. By rotating, the measurement head 16 may be rotated around the eyeball rotation X axis of the eye E to be examined.

With the above configuration, the drive mechanism 15 can move the measurement heads 16 individually or in conjunction with each other in the X, Y, and Z directions, and move the corresponding eyeball rotation point of the eye E to be examined. It can be rotated vertically and horizontally about the center, and each measuring head 16 can be moved to a position (orientation) corresponding to the rotation of the corresponding eye E to be examined. By adjusting the position of each measuring head 16, the driving mechanism 15 can cause the corresponding subject's eye E to diverge (divergence movement) or converge (convergence movement). As a result, the ophthalmologic apparatus 10 can perform a divergence motion test and a convergence motion test, perform a distance test and a near test in a state of binocular vision, and measure various characteristics of both eyes E to be examined.

Each measuring head 16 is provided with a deflecting member 26 , and information on the corresponding subject's eye E is acquired by the eye information acquisition unit 21 through the deflecting member 26 . As shown in FIG. 3, the ophthalmologic apparatus 10 adjusts the positions of the measurement heads 16 so that the deflecting members 26 are positioned corresponding to the left and right eyes E of the subject. With both eyes open (binocular vision state), information on the subject's eye E can be obtained simultaneously with both eyes. In addition, the ophthalmologic apparatus 10 changes the rotational posture of each measuring head 16 about the X-axis of eyeball rotation by the X-axis rotation drive unit 25, so that the corresponding subject eye E is viewed downward or upward. Information on eye examination E can be acquired. Then, the ophthalmologic apparatus 10 changes the rotational posture of each measuring head 16 about the Y-axis of eyeball rotation by the Y-axis rotation drive unit 24, and the corresponding eye to be inspected E is viewed horizontally. information can be obtained.

In addition, each measuring head 16 simultaneously changes its rotational posture symmetrically about the Y-axis of eyeball rotation of the corresponding eye E to be examined. The orientation of the optical axis L of the optical system of the eye information acquisition unit 21 can be changed in accordance with the changing visual axis (line-of-sight direction). The upper side of FIG. 3 shows a state in which the rotational posture of the binocular information acquisition unit 21 is adjusted so that the optical axes L from both eyes E to each deflection member 26 are parallel. In the upper state of FIG. 3, when each eye information acquiring unit 21 presents a fixation image Sf or the like to the corresponding eye E to be examined as will be described later, the subject looks at infinity in a state of binocular vision. The visual axis can be the same as in the state where the In addition, the lower side of FIG. 3 shows the rotational posture of the binocular information acquisition unit 21 so that the extended ends of the optical axes L from both eyes E to each deflection member 26 are directed toward the predetermined position P. is regulated. In the state shown in the lower part of FIG. 3, when each eye information acquiring unit 21 presents a fixation image Sf or the like to the corresponding eye E to be examined, the subject sees the predetermined position P with binocular vision. can be the same visual axis as In this way, the ophthalmologic apparatus 10 changes the rotational postures of the measurement heads 16 symmetrically at the same time, so that the visual axes of both eyes to be examined E are changed so as to converge or diverge. can be presented.

The base 11 is provided with a control unit 27 that is housed in a control box and that controls each part of the ophthalmologic apparatus 10 (see FIG. 1). As shown in FIG. 4, the control unit 27 includes the above-described eye information acquisition unit 21, each vertical driving unit 22 as the driving mechanism 15, each horizontal driving unit 23, each Y-axis rotating driving unit 24, and each X-axis driving unit 24. In addition to the rotation drive unit 25, the examiner controller 31, the subject controller 32, the storage unit 33, and the arm drive mechanism 34 are connected. In the ophthalmologic apparatus 10, power is supplied from a commercial power supply to a control unit 27 via a cable 28 (see FIGS. 1 and 2), and the control unit 27 controls the drive mechanism 15 and both measurement heads 16 (both eye information acquisition unit 21). to power the The control unit 27 can exchange information with the drive mechanism 15 and both measurement heads 16 (binocular information acquisition unit 21), controls their operations, and acquires information from them as appropriate.

The examiner controller 31 is used by the examiner to operate the ophthalmologic apparatus 10, and is communicably connected to the controller 27 by short-range wireless communication. Note that the examiner controller 31 is not limited to the configuration of the first embodiment as long as it is connected to the control unit 27 via a wired or wireless communication path. A portable terminal (information processing device) such as a tablet terminal or a smartphone is used as the examiner controller 31 of the first embodiment. Note that the controller for examiner 31 is not limited to a mobile terminal, and may be a notebook personal computer, a desktop personal computer, or the like, and may be configured by being fixed to the ophthalmologic apparatus 10. Not limited to configuration.

The examiner controller 31 includes a display section 35 consisting of a liquid crystal monitor. The display unit 35 has a display surface 35a (see FIG. 1, etc.) on which an image or the like is displayed, and a touch panel type input unit 35b superimposed thereon. Under the control of the control unit 27, the examiner controller 31 generates an anterior ocular segment image I (see FIG. 5) based on an image signal from an imaging device 41g provided in the observation system 41 described later, a measurement ring image described later, and a measurement ring image described later. A fundus image or the like is appropriately displayed on the display surface 35a. Further, the examiner controller 31 outputs to the control unit 27 operation information such as an alignment instruction and a measurement instruction which are displayed on the input unit 35 b under the control of the control unit 27 and input there.

The examinee controller 32 is used by the examinee to respond when acquiring various kinds of eye information of the eye to be examined E, and is connected to the control unit 27 via a wired or wireless communication path. . The subject controller 32 is, for example, an input device such as a keyboard, mouse, or joystick.

The control unit 27 appropriately controls the controller 31 for the examinee and the controller 32 for the examinee by expanding the program stored in the connected storage unit 33 or the built-in internal memory 27a on, for example, a RAM (random access memory). The operation of the ophthalmologic apparatus 10 is centrally controlled according to the operation. In the first embodiment, the internal memory 27a is composed of a RAM or the like, and the storage unit 33 is composed of a ROM (Read Only Memory), an EEPROM (Electrically Erasable Programmable ROM), or the like. In addition to the configuration described above, the ophthalmologic apparatus 10 is appropriately provided with a printer that prints the measurement results in response to a measurement completion signal or an instruction from the measurer, and an output unit that outputs the measurement results to an external memory or server.

Next, an optical configuration as an example of the eye information acquisition section 21 will be described with reference to FIG. As described above, the configurations of the right eye information acquisition section 21R and the left eye information acquisition section 21L are basically the same, and therefore the eye information acquisition section 21 will be simply described.

As shown in FIG. 5, the optical system of the eye information acquisition unit 21 includes an observation system 41, a target projection system 42, an eye refractive power measurement system 43, a Z alignment system 44, an XY alignment system 45, and a keratometric system 46. . The observation system 41 observes the anterior segment of the eye E to be examined, the target projection system 42 presents a target to the eye E to be examined, and the eye refractive power measurement system 43 measures the refractive power (refractive power) of the eye E to be examined. characteristics) are measured. The Z alignment system 44 and the XY alignment system 45 are provided to align the optical system with the eye E to be inspected. The Z alignment system 44 generates alignment information in the front-rear direction (Z direction) along the optical axis L of the observation system 41, and the XY alignment system 45 generates alignment information in the vertical and horizontal directions (Y direction, X direction) orthogonal to the optical axis L. generates alignment information for The keratometric system 46 provides measurements of corneal topography.

The observation system 41 has an objective lens 41a, a dichroic filter 41b, a half mirror 41c, a relay lens 41d, a dichroic filter 41e, an imaging lens 41f, and an imaging device 41g. The observation system 41 forms an image of the luminous flux reflected by the subject's eye E (anterior segment) via the objective lens 41a and the imaging lens 41f on the imaging element 41g (its light receiving surface). For this reason, the imaging device 41g detects (receives) an anterior ocular segment image I projected (projected) by a keratling luminous flux, a luminous flux of the alignment light source 44a, or a luminous flux of the alignment light source 45a (bright point image Br), which will be described later. . The control unit 27 causes the display surface 35a of the display unit 35 to display the anterior segment image I based on the image signal output from the imaging device 41g. A kerato system 46 is provided in front of the objective lens 41a.

Kerato system 46 has a kerato plate 46a and a kerato ring light source 46b. The keratoplate 46a has a plate shape provided with a slit concentric with respect to the optical axis L of the observation system 41, and is provided in the vicinity of the objective lens 41a. The keratizing light source 46b is provided in alignment with the slit of the keratoplate 46a. In the kerato system 46, a light flux from a lighted keratizing light source 46b passes through a slit of a keratoplate 46a, and a keratolight flux (for corneal curvature measurement) for measuring the shape of the cornea is directed to the eye E (its cornea Ec). A ring-shaped optotype) is emitted (projected). The keratling luminous flux is reflected by the cornea Ec of the eye E to be examined, and an image is formed on the imaging device 41g by the observation system 41. )do. Based on the image signal from the imaging device 41g, the control unit 27 displays the image of the measurement pattern on the display surface 35a, and performs keratometry for measuring the corneal shape (curvature radius) by a known technique. In Example 1, an example (kerat system 46) using a keratoplate 46a for measuring the curvature near the center of the cornea with one to three ring slits is shown as a corneal topography measuring system for measuring the corneal topography. However, a placido plate having multiple rings and capable of measuring the shape of the entire cornea may be used, or other configurations may be used, and the configuration is not limited to that of the first embodiment. A Z alignment system 44 is provided behind this kerato system 46 (kerato plate 46a).

The Z alignment system 44 has a pair of an alignment light source 44a and a projection lens 44b. A light beam from each alignment light source 44a is made into a parallel light beam by each projection lens 44b, and is projected through an alignment hole provided in a kerat plate 46a. The parallel light flux is projected (projected) onto the cornea Ec of . This parallel luminous flux is detected as alignment information of a bright spot (a bright spot image) projected onto the cornea Ec. Thereby, a target for alignment in the Z direction is projected onto the cornea Ec of the eye E to be examined. This visual target is detected as a virtual image (Purkinje image) due to corneal surface reflection. The control unit 27 moves the measuring head 16 back and forth by the horizontal driving unit 23 so that the ratio of the distance between the two bright spot images by the alignment light source 44a on the imaging device 41g and the diameter of the keratling image is within a predetermined range. Alignment in the front-rear direction (Z direction) along the optical axis L of the optical system of the eye information acquisition unit 21 is performed by moving in the direction (Z direction). Here, the control unit 27 may obtain the amount of misalignment from the ratio and display the amount of misalignment on the display surface 35a. Note that the alignment in the front-rear direction may be performed by adjusting the position of the right-eye measurement head 16R so that a bright spot image is focused by an alignment light source 45a, which will be described later. Alignment using a target by the Z alignment system 44 may include alignment in the X direction and the Y direction.

An XY alignment system 45 is provided in the observation system 41 . The XY alignment system 45 has an alignment light source 45a and a projection lens 45b, and shares the half mirror 41c, the dichroic filter 41b and the objective lens 41a with the observation system 41. The XY alignment system 45 projects the light flux from the alignment light source 45a onto the cornea Ec on the optical axis L as a parallel light flux through the objective lens 41a. This parallel luminous flux draws a virtual image (Purkinje image) due to the corneal surface reflection, and the bright point image Br, which is this virtual image, is detected by the observation system 41 (its imaging device 41g). This luminescent spot (luminescent spot image Br) is formed at a substantially intermediate position between the corneal vertex and the center of curvature of the cornea Ec. The control unit 27 drives the vertical driving unit 22 and the horizontal driving unit 23 based on the bright spots (luminescent spot images Br) to move the measuring head 16 in the horizontal direction (X direction) and the vertical direction (Y direction). Thus, alignment is performed in the vertical and horizontal directions (directions perpendicular to the optical axis L). At this time, the control unit 27 causes the display surface 35a to display an alignment mark AL, which serves as a guide for alignment, in addition to the anterior segment image I in which the bright spot image is formed. Further, the control unit 27 may be configured to perform control so as to start measurement when alignment is completed. The alignment light source 45a is a light-emitting diode that emits infrared light (for example, 940 nm) in order to prevent the subject from visually recognizing the alignment light source 45a during the alignment operation of the XY alignment system 45.

The visual target projection system 42 projects a visual target in order to fixate and cloud the subject's eye E, and presents the visual target on the fundus oculi Ef. The visual target projection system 42 has a display 42a, rotary prisms 42b and 42c, an imaging lens 42d, a moving lens 42e, a relay lens 42f, a field lens 42g, a mirror 42h, and a dichroic filter 42i. 41 a is shared with the observation system 41 . The display 42a presents a fixation target or a point-like target as a target for fixing the line of sight of the eye E to be examined, or displays characteristics of the eye E to be examined (visual acuity value, correction power (distance power, near power), etc.). ) to present a subjective inspection target for subjectively inspecting, or to present a fixation image Sf (see FIGS. 7, 9, etc.) for the convergence adjustment measurement process and the convergence limit measurement process described later. . The display 42 a can use EL (electroluminescence) or a liquid crystal display (LCD), and displays any image under the control of the control section 27 . The display 42a is movably provided along the optical axis at a position conjugate with the fundus Ef of the subject's eye E on the optical path of the target projection system 42 .

The rotary prisms 42b and 42c are used for adjusting the prism power and the prism base direction in the oblique examination, and are rotated independently by driving a pulse motor or the like. When the rotary prisms 42b and 42c are rotated in directions opposite to each other, the prism power is continuously changed, and when they are rotated integrally in the same direction, the prism base direction is continuously changed. The moving lens 42e is driven forward and backward along the optical axis by a drive motor. By moving the moving lens 42e toward the subject's eye E, the visual target projection system 42 can displace the refractive power to the minus side, and moving the moving lens 42e in the direction away from the subject's eye E, , the refractive power can be displaced to the positive side. As a result, the target projection system 42 can change the presentation distance of the target displayed on the display 42a by moving the moving lens 42e back and forth, that is, can change the presentation position of the target image. can be fixed and clouded. Therefore, the eye target projection system 42 can present an index for fixation and an index for subjective examination to the subject's eye E at an arbitrary presentation distance.

The eye refractive power measurement system 43 projects a measurement light beam onto the fundus oculi Ef of the eye E to be examined, and acquires the measurement light beam reflected by the fundus oculi Ef (its reflected light beam) as a measurement ring image described later. Allows measurement of eye refractive power. The eye refractive power measurement system 43 of Example 1 includes a ring-shaped light flux projection system 43A that projects a ring-shaped measurement pattern onto the fundus Ef of the eye to be examined E, and detects the reflected light of the ring-shaped measurement pattern from the fundus Ef ( and a ring-shaped light receiving system 43B for receiving an image. Note that the eye refractive power measurement system 43 has the above-described configuration. Other configurations may be used, and the configuration is not limited to that of the first embodiment. As an example of another configuration, a point-like spot light is projected onto the fundus oculi Ef as a measurement light beam, and the measurement light beam reflected by the fundus oculi Ef (the reflected light beam) passes through a ring-shaped slit or a lens to form a ring-shaped light beam. A light beam for acquiring a measurement ring image can be cited as the light flux.

The ring-shaped beam projection system 43A has a reflector light source unit 43a, a relay lens 43b, a pupil ring diaphragm 43c, a field lens 43d, a perforated prism 43e, and a rotary prism 43f. The observation system 41 shares the dichroic filter 41b and the objective lens 41a. The reflector light source unit 43a has, for example, a reflector measurement light source 43g for reflector measurement using an LED, a collimator lens 43h, a conical prism 43i, and a ring pattern forming plate 43j. It is integrally movable along the optical axis of the force measuring system 43 .

The ring-shaped light receiving system 43B has a hole portion 43p of a holed prism 43e, a field lens 43q, a reflecting mirror 43r, a relay lens 43s, a focusing lens 43t, and a reflecting mirror 43u. The dichroic filter 41e, the imaging lens 41f, and the imaging element 41g are shared with the observation system 41, the dichroic filter 42i is shared with the target projection system 42, and the rotary prism 43f and perforated prism 43e are shared with the ring-shaped beam projection system 43A. do.

The eye refractive power measurement system 43 measures the eye refractive power of the subject's eye E under the control of the control unit 27 in the eye refractive power measurement mode as follows. First, the reflector measurement light source 43g of the ring-shaped beam projection system 43A is turned on, and the reflector light source unit 43a of the ring-shaped beam projection system 43A and the focusing lens 43t of the ring-shaped beam receiving system 43B are moved in the optical axis direction. be. In the ring-shaped luminous flux projection system 43A, the reflector light source unit 43a emits a ring-shaped measurement pattern, and the measurement pattern advances to the perforated prism 43e through the relay lens 43b, the pupil ring diaphragm 43c, and the field lens 43d. The light is reflected by the reflecting surface 43v and led to the dichroic filter 42i through the rotary prism 43f. The ring-shaped light beam projection system 43A projects the ring-shaped measurement pattern onto the fundus Ef of the subject's eye E by guiding the measurement pattern to the objective lens 41a through the dichroic filters 42i and 41b.

In the ring-shaped light receiving system 43B, the ring-shaped measurement pattern formed on the fundus oculi Ef is collected by the objective lens 41a, passed through the dichroic filter 41b, the dichroic filter 42i, and the rotary prism 43f to the hole 43p of the perforated prism 43e. proceed. In the ring-shaped light receiving system 43B, the measurement pattern passes through a field lens 43q, a reflecting mirror 43r, a relay lens 43s, a focusing lens 43t, a reflecting mirror 43u, a dichroic filter 41e, and an imaging lens 41f, and is transferred to an image sensor 41g. form an image. As a result, the imaging element 41g detects an image of the ring-shaped measurement pattern (hereinafter also referred to as a measurement ring image), and the measurement ring image is displayed on the display surface 35a of the display unit 35 as appropriate. Based on the measurement ring image (image signal from the imaging device 41g), the control unit 27 determines the spherical power S, the cylindrical power C (cylinder power), and the axis angle Ax (cylinder axis angle) as eye refractive power. method. The control unit 27 appropriately displays the calculated eye refractive power on the display surface 35a.

In the eye refractive power measurement mode, the control unit 27 causes the display 42a of the target projection system 42 to display a fixed fixation target. A luminous flux from the display 42a passes through rotary prisms 42b and 42c, an imaging lens 42d, a moving lens 42e, a relay lens 42f, a field lens 42g, a mirror 42h, a dichroic filter 42i, a dichroic filter 41b, and an objective lens 41a, and reaches the subject's eye E is projected onto the fundus Ef. The examiner or the control unit 27 performs alignment with the examinee fixating the presented fixed fixation target, and aligns the subject with the far point of the subject's eye E based on the results of the provisional measurement of the eye refractive power (ref). After moving the moving lens 42e, the moving lens 42e is moved to an out-of-focus position to create a cloudy state. As a result, the subject's eye E enters an accommodation resting state (a state in which the crystalline lens is removed from accommodation), and the eye refractive power is measured in the accommodation resting state.

The configurations of the eye refractive power measurement system 43, the Z alignment system 44, the XY alignment system 45, the keratometry system 46, and the like, and the principles of eye refractive power (ref), subjective examination, and corneal shape (kerat) measurement are known. Therefore, detailed description is omitted.

Under the control of the control unit 27, the ophthalmologic apparatus 10 acquires the eye information of the subject's eye E using the eye information acquisition unit 21 while performing auto-alignment (automatic alignment). Specifically, based on the alignment information from the Z alignment system 44 and the XY alignment system 45, the control unit 27 aligns the optical axis L of the eye information acquisition unit 21 (its optical system) with the axis of the eye E to be examined. A moving amount (alignment information) is calculated so that the distance of the eye information acquisition unit 21 with respect to the eye examination E becomes a predetermined working distance. Here, the working distance is a default value also called a working distance, and is the distance between the eye information acquisition unit 21 and the subject's eye E for appropriately measuring characteristics using the eye information acquisition unit 21 . The control unit 27 drives the driving mechanism 15 according to the movement amount to move the eye information acquiring unit 21 with respect to the eye E to be inspected, thereby moving the eye information acquiring unit 21 (measuring head 16) for the corresponding eye E to be inspected. are aligned in the XYZ directions.

After that, the control unit 27 drives the eye information acquisition unit 21 appropriately to acquire various types of eye information of the eye E to be examined. In the ophthalmologic apparatus 10, the eye information acquiring unit 21 is aligned with the eye to be examined E, the eye refractive power measuring system 43 is driven, and the eye to be examined E is measured by operating the controller for the examiner 31 manually, that is, by the examiner. Various types of eye information can also be acquired. In the ophthalmologic apparatus 10, when acquiring various types of eye information about the eye E to be examined, the subject can respond by operating the controller 32 for subject. assist. Due to this alignment in the XYZ directions, each measuring head 16 is aligned so that the central position of the guide groove of each of the Y-axis rotation drive section 24 and the X-axis rotation drive section 25 coincides with the eyeball rotation point of the eye E to be examined. It is rotatable about the center in the horizontal direction (rotating direction about the Y direction) and the vertical direction (rotating direction about the X direction). Then, the control unit 27 can acquire the three-dimensional position of the eyeball rotation point of each subject eye E based on the positions of the respective measuring heads 16 aligned in the XYZ directions.

The ophthalmologic apparatus 10 can perform a convergence adjustment measurement process (convergence adjustment measurement mode) and a convergence limit measurement process (convergence limit measurement mode) for obtaining the relationship between convergence and accommodation in the control unit 27. Here, in the eye to be examined, convergence, that is, shortening the distance for binocular vision, changes accommodation according to the change in the distance, and conversely, changing accommodation causes convergence accordingly. and are performed at the same time. When determining the relationship between convergence and accommodation, the ophthalmologic apparatus 10 sets the focal distance Df and the rotation angle α in the eye information acquisition unit 21 in accordance with the presentation position Pp of the fixation image Sf as the reference state Sb. (see FIG. 6, etc.). This reference state Sb is a state in which an eye to be examined (so-called normal eye) that can appropriately converge and adjust binocularly sees the fixation image Sf presented at the presentation position Pp.

Then, in the convergence adjustment measurement step, the amount of change in convergence from the reference state Sb in which the convergence and adjustment are set so that the normal eye appropriately binocularly sees the fixation image Sf presented at the presentation position Pp (hereinafter referred to as convergence At least one of the amount C) and the change amount of adjustment (hereinafter also referred to as adjustment amount A) is determined. In the convergence limit measurement step, the fixation image Sf is presented in the reference state Sb at the predetermined presentation position Pp, and the presentation position Pp is changed to the near side, thereby adjusting the adjustment at the predetermined presentation position Pp. A convergence limit position for adjustment at a predetermined presentation position Pp is obtained. Thus, both the convergence accommodation measuring process and the convergence limit measuring process obtain the relationship between the convergence and accommodation in the eye E to be inspected.

Here, in the convergence accommodation measurement process and the convergence limit measurement process, the ophthalmologic apparatus 10 makes the subject binocularly view the fixation image Sf presented in the reference state Sb, and performs measurement. It is assumed that the fixation image Sf is clearly visible. For this reason, the ophthalmologic apparatus 10 allows binocular vision to adjust convergence when the subject is wearing spectacles or contact lenses, or using a corrective lens (for example, a phoropter provided in each eye information acquisition unit 21). A measurement process and a congestion limit measurement process are performed.

As shown in FIG. 4, the control unit 27 has a measurement setting unit 27b, a congestion acquisition unit 27c, an adjustment acquisition unit 27d, and a notification setting unit 27e for the congestion adjustment measurement process (congestion adjustment measurement mode). In addition to the measurement setting unit 27b described above, the control unit 27 has a fusion limit measurement unit 27f for the convergence limit measurement process (convergence limit measurement mode).

The measurement setting unit 27b performs settings for measuring the amount of convergence C and the amount of adjustment A, and by appropriately driving each unit of the ophthalmologic apparatus 10, as shown in FIG. A reference state Sb is assumed. The presentation position Pp indicates the position where the fixation image Sf is presented for the measurement of the amount of convergence C and the amount of adjustment A, and can be an arbitrary distance. In the first embodiment, the presentation position Pp is set to two positions, a predetermined distant position (far point (presentation position Pp1)) and a predetermined near position (near point (presentation position Pp2)), for measuring the amount of congestion C. For example, the far point is 5 m and the near point is 0.3 m. Also, in the first embodiment, two presentation positions Pp are set for the measurement of the adjustment amount A: a presentation position Pp1 on the reference plane Pb and a presentation position Pp3 on the displacement plane Pd. , the presentation position Pp1 (reference plane Pb) is 5 m, and the presentation position Pp3 (displacement plane Pd) is 4 m (see FIG. 11).

In the reference state Sb, the rotation angle α of the eye information acquisition unit 21 (both measurement heads 16) having the target projection system 42 and the visual field are adjusted to the presentation distance Dp, which is the interval from both eyes E to the presentation position Pp. In this state, the focal distance Df of the fixation image Sf in the target projection system 42 is set. The rotation angle α is fixed at infinity in the direction of the optical axis L of the eye target projection system 42 (eye information acquisition unit 21) (the direction of the optical axis L from the subject's eye E to each deflection member 26). This angle is based on the state of displaying the image Sf (parallel to each other). The direction of the optical axis L can be adjusted by rotating both measuring heads 16 around the eyeball rotation point of the corresponding eye E, as described above. Therefore, when the rotation angle α is 0 (zero) degrees, the directions of both optical axes L are parallel, and the visual axis of the subject's eye E is set at infinity. The rotation angle α can be obtained from the interpupillary distance PD, which is the distance between the eyes E to be examined, and the presentation distance Dp, which is the distance from the eyes E to the presentation position Pp. That is, the rotation angle α can be obtained by tan ⁻¹ (PD/2Dp). The interpupillary distance PD may be obtained from the anterior segment image I or the position of alignment, or may be a general value (eg, 64 mm), and 64 mm is used in the first embodiment.

The in-focus distance Df is a state in which the fixation image Sf to be displayed is focused on the presentation position Pp, and can be indicated by the distance from each subject eye E to the presentation position Pp. The focusing distance Df can be obtained from the presentation distance Dp, which is the distance from the center position of both eyes E to the presentation position Pp, and the rotation angle α described above. That is, the focusing distance Df can be obtained by Dp/cosα. This focusing distance Df can be adjusted by moving the moving lens 42e in the target projection system 42. FIG.

Here, when the far point (presentation position Pp1) is 5 m (5000 mm), the turning angle α1 is 0.3667 degrees and the focal distance Df1 is 5000.1024 mm. Also, when the near point (presentation position Pp2) is 0.3 m (300 mm), the rotation angle α2 is 6.0885 degrees and the focal distance Df2 is 301.7018 mm. Note that this number of significant digits is described as an example to facilitate understanding, and may be set as appropriate.

The measurement setting unit 27b rotates both the measurement heads 16 about the eyeball rotation point of the eye to be examined E corresponding to the presentation position Pp, and presents it to the eye E to be examined. 21) is set, and the moving lens 42e in the target projection system 42 is moved to set the focal distance Df. As a result, the measurement setting unit 27b can set the fixation image Sf displayed at the presentation position Pp to the reference state Sb in which binocular vision is performed appropriately. An image Sf can be presented.

At this time, when measuring the amount of convergence C in the convergence adjustment measurement step, the left and right eyes E are presented with fixation images Sf that enable confirmation of whether or not binocular vision is being performed appropriately. The fixation image Sf is basically a pattern that does not easily stimulate fusion. This is because it is difficult to confirm whether or not the binocular vision is properly performed when the images are fused. A pattern that does not easily stimulate the fusion is a pattern that has no common parts or has as few common parts as possible in the fixation images Sf presented to the left and right eyes E to be examined. In addition, the position, brightness, size, and the like of the pattern that does not easily stimulate the fusion may be different from each other in the fixation images Sf presented to the left and right eyes E to be examined. This is because, if the patterns presented to the left and right eyes E to be examined are common, fusion is stimulated to superimpose the common patterns.

Further, the fixation image Sf is more preferably a pattern that enables confirmation of whether or not the positions viewed by the left and right eyes are the same. This is because, as will be described later, when measuring the amount of convergence C, the subject may determine whether or not the positions viewed by the left and right eyes are the same. Here, when binocular vision is properly performed, the visual axes (line-of-sight directions) of the left and right eyes E pass through the presentation position Pp, and two fixation images Sf presented to the left and right eyes E are displayed. are visible. Therefore, it is possible to confirm whether or not the visible positions of the two fixation images Sf match with the pattern that enables confirmation of whether or not the positions viewed by the left and right eyes are the same. I can give you something to do. And it is necessary to avoid that this coincidence is due to fusion.

In view of these, in the first embodiment, as shown in FIG. 7, a fixation image Sf1 presented to the left eye E to be examined and a fixation image Sf2 presented to the right eye E to be examined are set. ing. In this fixation image Sf1, a rod-shaped pattern M1 extending vertically is drawn in a pure white background at the center position in the horizontal direction when viewing FIG. 7 from the front and in the lower half in the vertical direction. In the fixation image Sf2, a rod-shaped pattern M2 extending vertically is drawn in the upper half of the vertical direction at the central position in the horizontal direction when viewing FIG. 7 from the front in a pure white background. The pattern M2 has the same thickness as the pattern M1 of the fixation image Sf1. Note that the positions of the pattern M1 and the pattern M2 may be reversed between the fixation image Sf1 and the fixation image Sf2. Further, the fixation image Sf1 and the fixation image Sf2 are not limited to the configuration of the first embodiment, as long as the image fusion is not easily stimulated, the background color, pattern, and drawn pattern may be appropriately set. Further, the pattern M1 and the pattern M2 may each be configured by vertically arranging a plurality of characters or figures, and are not limited to the configuration of the first embodiment.

The congestion acquisition unit 27c uses the fixation image Sf presented in the reference state Sb set by the measurement setting unit 27b to obtain the amount of congestion C at the presentation position Pp. First, the subject is asked how the fixation image Sf presented in the reference state Sb by the measurement setting unit 27b looks. At this time, the congestion acquisition unit 27c determines how the subject looks in response to the operation of the subject controller 32 by the subject or the operation of the examiner controller 31 by the examiner who has heard the appearance from the subject. Acquire information on whether the object is visible (information on how it looks). In this way, the first step of obtaining the amount of congestion C is performed while the subject confirms how the subject sees it, and is a so-called subjective measurement.

Here, when binocular vision is properly performed, as shown in the upper part of FIG. 8, the fixation image Sf1 and the fixation image Sf2 are entirely overlapped and blurred at the center position in the horizontal direction when viewed from the front. The pattern M1 and the pattern M2 appear to be aligned in the vertical direction. That is, during binocular vision, when the right eye to be examined E is appropriately adjusted and converged with respect to the presentation position Pp, the pattern M1 appears to be below the central position in the horizontal direction without blurring. . In addition, when the left eye to be examined E is appropriately adjusted and converged with respect to the presentation position Pp during binocular vision, the pattern M2 appears above the central position in the horizontal direction without blurring. Therefore, the fixation image Sf1 and the fixation image Sf2 are superimposed, and the pattern M1 and the pattern M2 appear to be aligned in the vertical direction. The congestion acquisition unit 27c, when the obtained information on the appearance in the reference state Sb is such that the pattern M1 and the pattern M2 are aligned in the vertical direction, the congestion is appropriately congested, so the reference Let the congestion amount C from the state Sb be 0 (zero).

In addition, when the binocular vision is not properly performed, as shown in the lower side of FIG. The image Sf2 appears to be shifted in the horizontal direction. That is, if each eye E is not converged during binocular vision, the fixation image Sf1 or the fixation image Sf2 does not exist at the center position in the left-right direction. In Example 1, since the fixation image Sf1 and the fixation image Sf2 are used, it can be confirmed from the position of the pattern M1 or the pattern M2 that it does not exist at the center position in the horizontal direction. The example shown in the lower part of FIG. 8 shows that the right eye E to be examined is appropriately converged and the left eye E to be examined is not properly converged, and the fixation image Sf1 is on the left side. Due to the shift, the pattern M1 appears shifted left from the center, and the pattern M2 appears in the center without the fixation image Sf2 shifting. In the lower example of FIG. 8, the eye E to be examined on the right side is appropriately congested, so the amount of convergence C is 0 (zero). On the other hand, since the fixation image Sf1 of the left eye E to be examined appears shifted leftward from the center, the amount of convergence C does not become 0 (zero).

If at least one of the two fixation images Sf1 and Sf2 (patterns M1 and M2) is displaced in the acquired information of appearance in the reference state Sb, the congestion acquisition unit 27c to understand that it is not congested with Then, the convergence acquisition unit 27c obtains a state in which the two fixation images Sf1 and Sf2, which appear to be displaced from each other in the reference state Sb as described above, can be viewed appropriately binocularly, that is, the two fixation images Sf1 and Sf2 are obtained as a whole. The amount of convergence C in each eye to be examined until the overlapping state (see the upper side of FIG. 8) is obtained. Here, in the first embodiment, since the fixation image Sf1 and the fixation image Sf2 are used, whether or not the pattern M1 and the pattern M2 are aligned in the vertical direction is determined as to whether or not the entirety of the pattern M1 and pattern M2 are aligned. You can check with Then, the convergence acquisition unit 27c obtains the amount of convergence C in each subject eye from the reference state Sb until the pattern M1 and the pattern M2 are aligned in a straight line. This congestion amount C can be obtained by various methods, and the first embodiment exemplifies four methods.

A first method obtains the amount of congestion C by changing the display position of the fixation image Sf1 (symbol M1) on the display 42a. In this method, the convergence acquisition unit 27c moves the position where the fixation image Sf1 is displayed on the display 42a to the center while the subject continues binocular vision in the reference state Sb (see the lower side of FIG. 8). A displacement amount d of the display position when the fixation image Sf1 becomes visible in the center is obtained. At this time, the congestion acquisition unit 27c may shift the position to be displayed by a predetermined program, or may shift the position to be displayed according to the operation of the examiner's controller 31 by the examiner. In Example 1, the fixation image Sf1 and the fixation image Sf2 are set as described above, and since the right eye to be examined is properly converged, it is directly below the pattern M2 positioned in the center in the horizontal direction. The display position of the fixation image Sf1 is changed until the pattern M1 moves up to and appears to be aligned vertically. At this time, the convergence acquisition unit 27c acquires the fixation image Sf1 in response to the subject's operation of the subject controller 32 or the subject's operation of the subject controller 31 after hearing from the subject about the appearance. is seen in the center. For this reason, the first method is a so-called subjective measurement, which is performed while the examinee confirms how the examinee sees it.

The convergence acquisition unit 27c of Example 1 obtains the prism value Δ from the displacement amount d, and uses this prism value Δ as the convergence amount C. FIG. As is generally known, the prism value is defined as 1Δ (prism) when displaced by a width of 1 cm with respect to a presentation distance Dp of 1 m (100 cm). The prism value is 0.5Δ when the displacement is 0.5 cm, 2Δ when the displacement is 2 cm, and 0.5Δ when the presentation distance Dp is 2 m. In the case of 0.5 m, the relationship is 2Δ. Based on the above definition, the convergence acquisition unit 27c can calculate the prism value Δ from the displacement amount d by using the presentation distance Dp when the fixation image Sf1 is presented. Let the amount of congestion be C.

The second method obtains the amount of congestion C by arranging the refraction member 51 in front of the left eye E to be examined, as indicated by the two-dot chain line in the lower diagram of FIG. 3 . The refracting member 51 refracts the traveling direction of light, and the amount of refracting can be adjusted. In the first embodiment, a rotary prism is used. In this method, the amount of refraction of the refracting member 51 is changed while the subject continues binocular vision in the reference state Sb. Find the amount of refraction. The convergence acquisition unit 27c acquires information on the refraction amount of the refraction member 51 electrically from the refraction member 51 or according to the operation of the examiner controller 31 by the examiner who changed the refraction amount of the refraction member 51 . Since this amount of refraction can be expressed as the prism value Δ described above, the convergence acquisition unit 27c can obtain the amount of convergence C in the same manner as in the first method. Incidentally, the rotary prisms 42b and 42c (see FIG. 5) in the target projection system 42 may be used as the refractive member 51. FIG. For this reason, the second method is a so-called subjective measurement, which is performed while the subject confirms how the subject looks.

A third method obtains the amount of convergence C by rotating the visual target projection system 42 (eye information acquisition unit 21 (both measurement heads 16)). In this method, the convergence acquisition unit 27c rotates the measurement head 16 while the subject continues binocular vision in the reference state Sb, thereby shifting the position where the fixation image Sf1 is visible to the center side. Then, the amount of change in the rotation angle α when the subject can see the fixation image Sf1 in the center is obtained. At this time, the convergence acquisition unit 27c may rotate the measuring head 16 according to a predetermined program, or may rotate the measuring head 16 according to the operation of the examiner controller 31 by the examiner. Then, the convergence acquisition unit 27c acquires the amount of change in the rotation angle α by acquiring a signal from the drive mechanism 15 that rotates the measurement head 16 . The convergence acquisition unit 27c obtains the prism value Δ from the amount of change in the rotation angle α, and uses this prism value Δ as the amount of convergence C, as in the first method. As described above, the congestion acquisition unit 27c can obtain the congestion amount C from the reference state Sb at the predetermined presentation position Pp. For this reason, the third method is a so-called subjective measurement, in which the examinee confirms how the examinee sees it.

The third method may be combined with the first method, that is, changing the display position of the fixation image Sf1 (symbol M1) on the display 42a. A third technique in this case is, for example, to rotate the measurement head 16 when the adjustment amount of the fixation image Sf1 on the display 42a exceeds a predetermined range from the center of the display 42a. The third method in this case can obtain the congestion amount C in a wider range than when only the change in the display position on the display 42a is used. In addition, the third method in this case can present the fixation image Sf1 within a predetermined range centered on the optical axis L in the target projection system 42 even when the amount of convergence C is large. The amount of congestion C can be obtained by using the fixation image Sf1 presented in this state.

A fourth method obtains the amount of congestion C by obtaining the line-of-sight direction from the anterior segment image I. In this method, while the subject continues binocular vision in the reference state Sb, the observation system 41 acquires the anterior segment image I in which the bright point image Br is formed by the XY alignment system 45 (Fig. 5). The convergence acquisition unit 27c acquires the anterior segment image I from the observation system 41, analyzes the anterior segment image I, and obtains the pupil center position and the position of the bright spot image Br. In addition, the convergence acquisition unit 27c, based on the fact that the bright point image Br is formed inward from the corneal vertex at a position half the radius of curvature of the cornea, determines the three-dimensional The original position is obtained, and the direction connecting the curvature center and the pupil center position is obtained. As a result, the convergence acquisition unit 27c obtains the three-dimensional position of the eyeball rotation point using the distance from the corneal vertex to the eyeball rotation point, and the direction connecting the pupil center position and the eyeball rotation point (curvature center) and the optical axis L The line-of-sight direction is obtained from the direction of . Then, the congestion acquisition unit 27c obtains the difference angle of the line-of-sight direction with respect to the reference state Sb from the rotation angle α and the line-of-sight direction in the reference state Sb. The convergence acquisition unit 27c uses this difference angle and the presentation distance Dp when the fixation image Sf1 is presented to obtain the prism value Δ as the amount of convergence C in the same manner as in the first method. Therefore, the fourth method does not require confirmation of the subject's vision, and is so-called objective measurement.

In the fourth method, the measurement head 16 is rotated as in the third method so that the line-of-sight direction is obtained, and whether or not the subject sees the fixation image Sf1 in the center may be asked. In this case, the measurement head 16 can be rotated quickly, and the time required can be shortened. The fourth method in this case is a combination of objective measurement in which the subject moves without confirming how they see, and subjective measurement performed while the subject confirms how they see. Become.

The fourth method may be combined with the first method, that is, changing the display position of the fixation image Sf1 (symbol M1) on the display 42a. A fourth technique in this case is to change the display position of the fixation image Sf1 on the display 42a so as to achieve the obtained line-of-sight direction, and determine whether the subject can see the fixation image Sf1 in the center in that state. shall be asked. In this case, the display position can be changed quickly, and the required time can be shortened. The fourth method in this case is a combination of objective measurement in which the subject moves without confirming how they see, and subjective measurement performed while the subject confirms how they see. Become.

Furthermore, in the first to third methods, the convergence acquisition unit 27c obtains the line-of-sight direction from the anterior segment image I as in the fourth method, and displays the line-of-sight direction on the display surface 35a or the like. may be presented to With such a configuration, the examiner grasps the actual line-of-sight direction in the state in which the subject requests that the fixation image Sf1 can be seen in the center by subjective measurement using the first to third methods. This can be used as a reference for determining whether or not the binocular vision has been appropriately achieved.

Here, the convergence acquisition unit 27c, in each method, a predetermined program, and in the case of subjective measurement, operation of the subject controller 32 by the subject indicating whether or not binocular vision is possible. can be used to obtain the congestion amount C, so that it can be automated. In particular, in the case of the fourth technique, since it is an objective measurement, it can be automated more easily. This is particularly effective when the ophthalmologic apparatus 10 is installed at a remote location.

The adjustment acquisition unit 27d obtains the adjustment amount A at the presentation position Pp using the fixation image Sf presented in the reference state Sb set by the measurement setting unit 27b. Obtaining this adjustment amount A is based on the premise that the fixation image Sf presented in the reference state Sb at the predetermined presentation position Pp is fused. This is because, as will be described later, the adjustment amount A is the amount of change in adjustment when the presentation position Pp is changed from the reference plane Pb to the displacement plane Pd (FIG. 12).

Therefore, when measuring the adjustment amount A in the convergence adjustment measurement process, the measurement setting unit 27b presents the fixation images Sf that are easily fused to the left and right eyes E to be examined. The fixation image Sf is basically a pattern that easily stimulates fusion, and one example is that the fixation images Sf presented to the left and right eyes E to be examined have many common parts or are the same. . In Example 1, as shown in FIG. 9, a fixation image Sf3 presented to the left eye E and a fixation image Sf4 presented to the right eye E are set. This fixation image Sf3 has a carrot pattern M3 drawn in the center in the horizontal direction in a pure white background. A pattern M4 is drawn. The pattern M3 and the pattern M4 are the same pattern and are drawn at the same positions, and the fixation image Sf3 and the fixation image Sf4 are the same. As a result, when both fixation images Sf3 and Sf4 are presented in the reference state Sb at the predetermined presentation position Pp set by the measurement setting unit 27b, as shown in FIG. Both fixation images Sf3 and Sf4 are fused. As long as the fixation image Sf3 and the fixation image Sf4 are easy to fuse, for example, some pattern or the like may be drawn on the background to stimulate the fusion. The pattern to be drawn may be appropriately set, and is not limited to the configuration of the first embodiment.

In addition, in Example 1, the fixation image Sf3 is provided with a pattern M5, and the fixation image Sf4 is provided with a pattern M6, in order to confirm whether fusion is possible. The pattern M5 is drawn in the lower left corner of the fixation image Sf3 and is a red circle. The pattern M6 is drawn in the lower right corner of the fixation image Sf4 and is a green circle. As shown in FIG. 10, the pattern M5 and the pattern M6 are superimposed so that the pattern M3 and the pattern M4 match. makes it possible to distinguish whether it is due to fusion or suppression when answering. That is, in the case of fusion, both the pattern M5 and the pattern M6 are visible, but in the case of suppression, only one of the pattern M5 and the pattern M6 is visible. . In addition, if the pattern M5 and the pattern M6 are both visible when they are fused, and only one is visible when they are suppressed, color The shape and location may be appropriately set, and are not limited to the configuration of the first embodiment.

As shown in FIG. 11, the adjustment acquisition unit 27d defines an adjustment amount A as an adjustment change amount when the presentation position Pp is changed from the reference plane Pb to the displacement plane Pd. In order to obtain this adjustment amount A, the reference plane Pb and the displacement plane Pd are set as follows. In the example of a 3D movie, let the plane on which the movie screen is set for the subject be the reference plane Pb. Then, when the fixation image Sf displayed on the screen is stereoscopically viewed (3D image), the display surface (display position) of the fixation image Sf projected from the screen to the front side, or the display surface (display position) of the fixation image Sf to be projected from the screen or recessed to the back side from the screen. Let the display plane (display position) of the fixation image Sf shown in . In the example shown in FIG. 11, the displacement plane Pd is in a state of protruding forward by 1 m from the reference plane Pb (screen).

First, in the vergence adjustment measurement step, in order to measure the adjustment amount A, the measurement setting unit 27b presents the fixation image Sf in the reference state Sb at the presentation position Pp that matches the reference plane Pb. Then, the adjustment acquisition unit 27d confirms that the fixation image Sf presented in the reference state Sb is fused by the measurement setting unit 27b. Here, in Example 1, since the fixation image Sf3 and the fixation image Sf4 are presented in the reference state Sb, it is easy to fuse them. Therefore, it is easy to judge whether or not the image is fused. At this time, the adjustment acquisition unit 27d determines how the subject looks in accordance with the operation of the subject controller 32 by the subject or the operation of the subject controller 31 by the examiner who has heard about the appearance from the subject. Acquire information on whether the object is visible (information on how it looks). Then, in the fusion state, the accommodation acquisition unit 27d uses the eye refractive power measurement system 43 to measure the eye refractive power P1 (unit: diopter) of each eye E to be examined. In this way, the first step in obtaining the adjustment amount A is a so-called subjective measurement performed while the subject confirms how the subject sees, an objective measurement in which the subject moves without confirming the subject's appearance, is a combination of

Thereafter, the adjustment acquisition unit 27d changes the presentation position Pp from the presentation position Pp1 on the reference plane Pb to the presentation position Pp3 on the displacement plane Pd. 21 (both measuring heads 16) are changed. That is, from the rotation angle α1 corresponding to the presented distance Dp1 to the reference plane Pb to the rotation angle α3 matched to the presentation distance Dp3 to the displacement plane Pd, both the measuring heads 16 are moved to the corresponding eyeball rotation point of the eye E to be examined. , and the left and right rotation angle α is gradually increased at the same time. Also, the focal distance Df of the fixation image Sf in the target projection system 42 is set to a focal distance Df3 that matches the presentation distance Dp1 to the reference plane Pb. At this time, the adjustment acquisition unit 27d may perform the rotation of the eye information acquisition unit 21 and the movement of the moving lens 42e according to a predetermined program. good too. As a result, the adjustment acquisition unit 27d causes the line of sight to intersect at the presentation position Pp3 on the displacement plane Pd, and displays the fixation image Sf4 to be presented to the right eye E to be examined at the presentation position Pp4 on the reference plane Pb. A fixation image Sf3 to be presented to the left eye E is displayed at the presentation position Pp5 on the plane Pb. At this time, since the fixation image Sf3 and the fixation image Sf4 are supposed to stimulate fusion, the subject adjusts both eyes to achieve a fusion state as shown in FIG. In this state, the accommodation acquisition unit 27d uses the eye refractive power measurement system 43 to measure the eye refractive power P2 (unit: diopter) of each eye E to be examined. Then, the accommodation acquisition unit 27d subtracts the eye refractive power P2 in the state where the fixation images Sf3 and Sf4 are fused on the displacement plane Pd from the eye refractive power P1 in the reference state Sb. , an adjustment amount A (in units of diopters) for each eye to be examined is obtained. Thus, obtaining the adjustment amount A is a combination of subjective measurement and objective measurement. Thereby, the adjustment obtaining unit 27d can obtain the adjustment amount A from the reference state Sb at the predetermined presentation position Pp (on the reference plane Pb in this example).

Here, since the adjustment acquisition unit 27d can obtain the adjustment amount A using a predetermined program and the operation of the subject controller 32 by the subject, automation can be achieved. This is particularly effective when the ophthalmologic apparatus 10 is installed at a remote location.

The notification setting unit 27e sets a mode in which the display unit 35 notifies the congestion amount C obtained by the congestion acquisition unit 27c and the adjustment amount A obtained by the adjustment acquisition unit 27d. As one aspect, the notification setting unit 27e obtains the AC/A ratio. The AC/A ratio (ratio of accommodative convergence to accommodation) indicates accommodative convergence per unit accommodation. This AC/A ratio is obtained as follows. First, the notification setting unit 27e is the amount of congestion C1 (prism value Δ) at the near point (0.3 m in Example 1) and the amount of congestion C2 (prism value Δ) at the far point (5 m in Example 1) and are acquired from the congestion acquisition unit 27c. Then, the notification setting unit 27e obtains D (diopter (3.3 (1/0.3) in the first embodiment)) indicating the adjustment at the near point. Then, the notification setting unit 27e obtains the AC/A ratio using the following equation (1) or (2). The formula (1) uses the gradient method, and the formula (2) uses the heterophoric method.

AC/A ratio = (C1-C2)/D (1)

AC/A ratio = PD + (C1-C2)/D (2)

In addition, the notification setting unit 27e obtains the CA/C ratio as another aspect. The CA/C ratio (ratio of convergence accommodation to convergence) indicates the convergence accommodation per unit convergence. This CA/C ratio is obtained as follows. First, the notification setting unit 27e acquires the amount of congestion C3 (prism value Δ) on the displacement plane Pd and the amount of congestion C1 (prism value Δ) on the reference plane Pb from the convergence acquisition unit 27c, The adjustment amount A when changing the rotation angle α from the reference plane Pb (rotation angle α1) to the displacement plane Pd (rotation angle α3) is acquired from the adjustment acquisition unit 27d. Then, the notification setting unit 27e obtains the CA/C ratio using the following equation (3).

CA/C ratio = A/(C3-C1) (3)

Furthermore, the notification setting unit 27e creates a graph using the congestion amount C and the adjustment amount A as another aspect. The notification setting unit 27e acquires, for example, the congestion amount C from the reference state Sb at a plurality of presentation positions Pp from the congestion acquisition unit 27c, and creates a graph in which the horizontal axis is the presentation distance Dp and the vertical axis is the congestion amount C. create. This graph makes it easy to grasp how the congestion amount C changes with respect to the change in the presentation distance Dp. In this case, the congestion acquisition unit 27c acquires the amount of congestion C at presentation distances Dp other than the two points, the far point and the near point, and the notification setting unit 27e acquires each congestion amount C to obtain more detailed information. graphs can be created. Further, the notification setting unit 27e, for example, changes the rotation angle α from the adjustment acquisition unit 27d from the reference state Sb at the presentation position Pp on the reference plane Pb to match the presentation position Pp3 on the displacement plane Pd. Each adjustment amount A is acquired, and a graph is created with the presentation distance Dp corresponding to the displacement plane Pd on the horizontal axis and the adjustment amount A on the vertical axis. This graph makes it easy to grasp how the adjustment amount A changes with respect to the change in the presentation distance Dp (displacement plane Pd). In this case, the adjustment acquisition unit 27d sets a plurality of displacement planes Pd to acquire adjustment amounts A, and the notification setting unit 27e acquires each adjustment amount A, thereby creating a more detailed graph. can.

Next, as another aspect, the notification setting unit 27e displays the congestion amount C and the adjustment amount A numerically. In this case, the notification setting unit 27e displays the congestion amount C and the adjustment amount A together with the respective presentation positions Pp, so that the relationship between the congestion amount C and the adjustment amount A can be easily grasped. .

The control unit 27 causes the display unit 35 to notify the congestion amount C and the adjustment amount A according to the mode created by the notification setting unit 27e. As a result, the ophthalmologic apparatus 10 provides numerical values of the convergence amount C and the adjustment amount A at each presentation position Pp, graphs showing them, AC/A ratio, CA/C ratio, as an example of the relationship between convergence and accommodation. 1 item can be notified. Below, the numerical values of the congestion amount C and the adjustment amount A are the first item, the graphs showing them are the second item, the AC / A ratio is the third item, and the CA / C ratio is 4 The first item. A series of operations for obtaining at least one of the four items by the measurement setting unit 27b, the congestion acquisition unit 27c, the adjustment acquisition unit 27d, and the notification setting unit 27e obtain the congestion amount C and the adjustment amount A from the reference state Sb. It becomes a congestion adjustment measurement step (congestion adjustment measurement mode).

Next, the fusion limit measuring unit 27f presents the fixation image Sf in the reference state Sb at the distant presentation position Pp set by the measurement setting unit 27b, and while maintaining the presented state, moves the presentation position Pp from a distance. The congestion limit measurement process (congestion limit measurement mode) is performed by changing to near. In this convergence limit measurement step, when changing the presentation position Pp from far to near, it measures to what position on the near side the fusion is possible, so in the reference state Sb at the far presentation position Pp It is assumed that the presented fixation image Sf is fused. Therefore, in the convergence limit measurement step, the fixation images Sf, which are easily fused, are presented to the left and right eyes to be examined E. In the first embodiment, the fixation images Sf3 and Sf4 shown in FIG. shall be

The fusion limit measurement unit 27f moves both measurement heads 16 from the state in which the fixation image Sf is presented in the reference state Sb at the distant presentation position Pp set by the measurement setting unit 27b to the corresponding eyeball rotation point of the subject's eye E. Rotate to the center and gradually increase the left and right rotation angles α at the same time. As a result, the presentation position Pp of the fixation image Sf changes from the presentation position Pp1 shown in FIG. 6 toward the presentation position Pp2. At this time, the fusion limit measurement unit 27f may gradually increase the left and right rotation angles α simultaneously according to a predetermined program, and simultaneously increase the left and right rotation angles α according to the examiner's operation of the examiner controller 31. It can be increased gradually. Further, the fusion limit measuring unit 27f maintains a state in which the focal distance Df of the optotype projection system 42 is set with respect to the distant presentation position Pp when gradually increasing the left and right rotation angles α at the same time. Do not change the focusing distance Df. As a result, it is conceivable that the fixation image Sf3 and the fixation image Sf4 will gradually blur even if the fusion state is maintained. Since we are looking for the limit of the image, there is no problem.

Then, the fusion limit measurement unit 27f gradually increases the left and right rotation angles α at the same time as described above, and stops the gradual increase of the left and right rotation angles α when the subject can no longer fuse. The left and right rotation angles α are stored. At this time, the fusion limit measurement unit 27f obtains the information that the subject can no longer fuse, by the operation of the subject controller 32 by the subject, or by the examiner who heard the appearance from the subject. Acquired by operating the examiner controller 31 . Then, the fusion limit measurement unit 27f calculates the prism value Δ and the presentation position Pp that become the rotation angle α from the information on the left and right rotation angles α.

The control unit 27 causes the display unit 35 to notify at least one of the left and right rotation angle α, the prism value Δ, and the presentation position Pp stored by the fusion limit measurement unit 27f as the limit point of fusion, that is, the limit position of convergence. . Thereby, the ophthalmologic apparatus 10 can report the limit position of convergence as an example of the relationship between convergence and accommodation. A series of operations by the measurement setting unit 27b and the fusion limit measurement unit 27f constitute a convergence limit measurement step (convergence limit measurement mode) for determining the convergence limit position for adjustment at a predetermined presentation position Pp.

Next, using the ophthalmologic apparatus 10, measurement control processing (measurement control method) will be described with reference to FIG. This measurement control process is executed by the control section 27 based on a program stored in the storage section 33 or the built-in internal memory 27a. Each step (each process) of the flow chart of FIG. 12 will be described below. In the flowchart of FIG. 12, the ophthalmologic apparatus 10 is activated, the browser or application of the examiner's controller 31 is launched, the display screen 35a is displayed, and the relationship between convergence and accommodation is selected in the input section 35b. is started by At this time, the subject is sitting on a chair or the like, and the forehead is applied to the forehead support portion 17 . In the flowchart of FIG. 12 of the first embodiment, each step (each process) is performed simultaneously by a pair of measurement heads 16 (binocular information acquisition unit 21), and measurements are performed simultaneously in the state of binocular vision. I am assuming.

In step S1, it is determined whether or not the congestion adjustment measurement process is to be performed. If YES, the process proceeds to step S2, and if NO, the process proceeds to step S6. In step S1, whether to perform a congestion adjustment measurement step for obtaining the congestion amount C and adjustment amount A from the reference state Sb, or a congestion limit measurement step for obtaining the congestion limit position for adjustment at a predetermined presentation position Pp set make a decision as to whether to This determination is made based on the operation information given to the subject controller 32 . Here, in the first embodiment, as the congestion adjustment measurement step, acquisition of the congestion amount C and the adjustment amount A, acquisition of the congestion amount C and the adjustment amount A graph, acquisition of the AC / A ratio, acquisition of the CA / C ratio Four items can be executed. Therefore, in step S1, when at least one of the four items as the congestion adjustment measurement process is selected by the operation information provided to the subject controller 32, it is determined that the congestion adjustment measurement process is to be performed. . In addition, in step S1, a plurality of the four items may be selected.

In step S2, settings are made for measuring the amount of congestion C and the amount of adjustment A, and the process proceeds to step S3. In step S2, first, auto-alignment is executed to align the optical axis L of the optical system of the eye information acquisition unit 21 with the visual axis (line-of-sight direction) of the eye E to be examined. Let state be Sb. Here, in Example 1, the relationship between convergence and accommodation is obtained from the four items described above. Therefore, in the case of the first item above, the congestion acquisition unit 27c and the adjustment acquisition unit 27d measure the congestion amount C and the adjustment amount A at an arbitrary presentation position Pp, and the set presentation position Pp number of measurements. In addition, in the case of the second item above, the congestion amount C and the adjustment amount A at an arbitrary presentation position Pp are measured by the congestion acquisition unit 27c and the adjustment acquisition unit 27d, and depending on the required fineness Measure the number of presentation positions Pp set by Furthermore, in the case of the third item, the congestion level C is measured at the far point and the near point by the congestion acquisition unit 27c, and the congestion level C is measured twice. In the case of the fourth item above, the congestion acquisition unit 27c measures the amount of congestion C on the reference plane Pb and the displacement plane Pd, and the adjustment amount when the displacement plane Pd is set from the reference plane Pb The measurement of A is performed by the adjustment acquisition unit 27d, so that the congestion amount C is measured twice and the adjustment amount A is measured once. For this reason, the predetermined presentation positions Pp differ in the position and the number to be set according to the selected item.

In step S3, the amount of congestion C and the amount of adjustment A are obtained, and the process proceeds to step S4. In step S3, depending on the item selected in step S1, the congestion acquisition unit 27c obtains the congestion amount C from the reference state Sb at the presentation position Pp set in step S2, or the adjustment acquisition unit 27d obtains the An adjustment amount A from the reference state Sb at the presentation position Pp set in S2 is obtained. In this step S3, when steps S4→S2→S3 described later are repeated, the congestion amount C and the adjustment amount A are obtained at a different presentation position Pp from the congestion amount C and the adjustment amount A obtained in the previous step S3.

In step S4, it is determined whether or not the measurement has been completed. If YES, the process proceeds to step S5, and if NO, the process returns to step S2. In step S4, it is determined whether or not the number of times the congestion amount C and adjustment amount A are obtained in step S3 is equal to the number of presentation positions Pp set in step S2. If equal, it is determined that the measurement is completed, and if not equal, that is, if the number of times the congestion amount C or the adjustment amount A is obtained is less than the set number of presentation positions Pp, the measurement is completed. judge that it is not.

In step S5, the notification mode is set, and the process proceeds to step S8. In step S5, the notification setting unit 27e sets the notification mode corresponding to the item selected in step S1 based on the congestion amount C and the adjustment amount A obtained by the congestion acquisition unit 27c and the adjustment acquisition unit 27d in step S3. do. That is, in step S5, the notification setting unit 27e uses the congestion amount C and the adjustment amount A obtained in step S3 to obtain the numerical values of the congestion amount C and the adjustment amount A, the graph of the congestion amount C and the adjustment amount A, AC/ The A ratio and the CA/C ratio (indications indicating them) are appropriately set.

In step S6, settings are made to obtain the congestion limit position, and the process proceeds to step S7. In step S6, first, auto-alignment is executed to align the optical axis L of the optical system of the eye information acquisition unit 21 with the visual axis (line of sight) of the eye E to be examined. Let state be Sb. Here, in Example 1, as the convergence limit measurement step, the convergence limit position for adjustment at the far point (5 m in Example 1) presentation position Pp is obtained, so according to the far point presentation position Pp A reference state Sb is assumed.

In step S7, the congestion limit position is obtained, and the process proceeds to step S8. In step S7, the fusion limit measurement unit 27f gradually increases the left and right rotation angle α from the reference state Sb at the far point presentation position Pp set in step S6, and the subject can no longer fuse. The presentation position Pp at the rotation angle α is acquired as the convergence limit position. At this time, in step S7, the focusing distance Df of the target projection system 42 is kept at the far point (5 m) and is not changed.

In step S8, the relationship between congestion and accommodation is reported, and this measurement control process ends. In this step S8, the control unit 27 sets the notification mode set by the notification setting unit 27e in step S5 in the case of the convergence adjustment measurement process, and the fusion limit measurement unit 27f in step S7 in the case of the convergence limit measurement process. The obtained convergence limit position is appropriately displayed on the display surface 35a.

In this way, the ophthalmologic apparatus 10 can obtain the relationship between convergence and accommodation in each state of the subject's eye E during binocular vision. Therefore, since the ophthalmologic apparatus 10 can obtain the relationship between convergence and accommodation in a more natural state, it is possible to obtain an appropriate relationship between convergence and accommodation, and it is possible to prevent poor visual performance, eyestrain, and the like. It can greatly contribute to obtaining the cause accurately.

In addition, the ophthalmologic apparatus 10 has a configuration in which each measuring head 16 provided with an eye information acquisition unit 21 that presents a fixation image Sf to the left and right eyes E to be examined can be rotated around the eyeball rotation points of the corresponding eyes E to be examined E. By changing the focal distance Df of the fixation image Sf in the eye information acquisition unit 21 and the rotation angle α of the eye information acquisition unit 21, the relationship between convergence and accommodation is obtained. Therefore, the ophthalmologic apparatus 10 can obtain the relationship between convergence and accommodation in a more natural state with a simple small configuration and simple control. That is, the ophthalmologic apparatus 10 adjusts the focus distance Df and the rotation angle α in both the measuring heads 16 and the eye information acquisition unit 21 (so-called internal target method) in a natural state. It can be configured, and the practicality can be improved.

Further, the ophthalmologic apparatus 10 appropriately sets the focal distance Df of the fixation image Sf in the eye information acquisition unit 21 configured as described above and the rotation angle α of the eye information acquisition unit 21, thereby reducing the AC/A ratio and the CA /C ratio can be determined. Therefore, the ophthalmologic apparatus 10 can easily and appropriately obtain the AC/A ratio and the CA/C ratio, which are generally difficult to obtain accurately and require complicated measurements.

The ophthalmologic apparatus 10 changes the rotation angle α in the eye information acquisition unit 21 from the above reference state Sb to change the presentation position Pp of the fixation image Sf toward the near side, thereby adjusting the predetermined presentation position Pp. It is possible to obtain the limit position of congestion for Therefore, the ophthalmologic apparatus 10 can obtain the limit position of convergence with respect to accommodation at the predetermined presentation position Pp in a state of binocular vision.

The ophthalmic device 10 of the first embodiment of the ophthalmic device according to the present disclosure can obtain the following effects.

In the ophthalmologic apparatus 10, the control unit 27 presents the fixation image Sf in the eye information acquisition unit 21, and calculates the focal distance Df of the fixation image Sf in the eye information acquisition unit 21 and the rotation angle α of the eye information acquisition unit 21. By changing , the relationship between convergence and accommodation in the subject's eye E is obtained. Therefore, the ophthalmologic apparatus 10 can obtain the relationship between convergence and accommodation in a state very close to the state in which the subject naturally sees binocularly. Compared to the method of switching to , the relationship between vergence and accommodation can be properly measured.

The ophthalmologic apparatus 10 presents the fixation image Sf in the reference state Sb in which the control unit 27 sets the focal distance Df and the rotation angle α in the eye information acquisition unit 21 so as to match the presentation position Pp of the fixation image Sf. do. Therefore, the ophthalmologic apparatus 10 can set the state in which the normal eye sees the fixation image Sf presented at the presentation position Pp binocularly as the reference state Sb. Then, the ophthalmologic apparatus 10 obtains the amount of change in convergence (the amount of convergence C) from the reference state Sb to the state in which the fixation image Sf can be viewed properly binocularly. Therefore, since the ophthalmologic apparatus 10 obtains the congestion amount C based on the reference state Sb, the congestion amount C can be obtained more appropriately.

The ophthalmologic apparatus 10 is in the reference state Sb in which the control unit 27 sets the focal distance Df and the rotation angle α in the eye information acquisition unit 21 by matching the presentation position Pp of the fixation image Sf on the reference plane Pb. A fixation image Sf is presented, and a change amount of adjustment (adjustment amount A) is obtained when the rotation angle α is changed by fitting the presentation position Pp of the fixation image Sf from the reference plane Pb to the displacement plane Pd. . For this reason, the ophthalmologic apparatus 10 uses the reference state Sb as a reference, presents the fixation image Sf on the reference plane Pb at that time, and adjusts the adjustment amount A in a state in which the rotation angle α is aligned with the displacement plane Pd. is obtained, the adjustment amount A can be obtained more appropriately.

The ophthalmologic apparatus 10 is in a state in which the eye information acquisition unit 21 presents the eye E to be examined using the target projection system 42 with the fixation image Sf displayed on the display 42a. Then, in the ophthalmologic apparatus 10, the controller 27 changes the display position of the fixation image Sf on the display 42a to obtain the amount of change in congestion (congestion amount C). Therefore, the ophthalmologic apparatus 10 can appropriately obtain the amount of congestion C with a simple configuration.

In the ophthalmologic apparatus 10, the control unit 27 changes the rotation angle α of the eye information acquisition unit 21 to obtain the amount of change in convergence (congestion amount C). Therefore, the ophthalmologic apparatus 10 can easily obtain the amount of convergence C in a larger range, and can obtain the amount of convergence C using the fixation image Sf1 presented in good condition.

In the ophthalmologic apparatus 10, the control unit 27 changes the amount of refraction in the refraction member 51 that refracts the axis of the eye information acquisition unit 21, thereby obtaining the amount of change in convergence (the amount of convergence C). Therefore, the ophthalmologic apparatus 10 can easily obtain the convergence amount C. FIG.

In the ophthalmologic apparatus 10, the controller 27 obtains the amount of change in convergence (the amount of convergence C) from the line-of-sight direction of the subject's eye E when the fixation image Sf is presented in the reference state Sb. Therefore, the ophthalmologic apparatus 10 can easily obtain the congestion amount C without requiring a response from the subject.

The ophthalmologic apparatus 10 determines the AC/A ratio based on the amount of change in convergence when the control unit 27 makes the presentation position Pp far and the amount of change in convergence when the presentation position Pp is made near. demand. Therefore, the ophthalmologic apparatus 10 can easily and appropriately obtain the AC/A ratio, which is generally difficult to obtain accurately and requires complicated measurements.

The ophthalmologic apparatus 10 calculates the adjustment change amount (adjustment amount A) obtained by the control unit 27, the congestion change amount (congestion amount C) when the presentation position Pp is on the reference plane Pb, and the presentation position Pp. The CA/C ratio is obtained based on the amount of change in congestion (congestion amount C) when the rotation angle α is changed so as to be on the displacement plane Pd. Therefore, the ophthalmologic apparatus 10 can easily and appropriately obtain the CA/C ratio, which is generally difficult to obtain accurately and requires complicated measurements.

The ophthalmologic apparatus 10 presents the fixation image Sf in the reference state Sb in which the control unit 27 sets the focal distance Df and the rotation angle α in the eye information acquisition unit 21 so as to match the presentation position Pp of the fixation image Sf. The presentation position Pp of the fixation image Sf is moved closer by changing the rotation angle α of the eye information acquisition unit 21 from the reference state Sb. Therefore, the ophthalmologic apparatus 10 can easily and appropriately obtain the convergence limit position for adjustment at the predetermined presentation position Pp.

Therefore, the ophthalmologic apparatus 10 as an embodiment of the ophthalmologic apparatus according to the present disclosure can appropriately measure the relationship between convergence and accommodation.

The ophthalmologic apparatus of the present disclosure has been described above based on Example 1, but the specific configuration is not limited to Example 1, and does not depart from the gist of the invention according to each claim. Design changes, additions, etc. are permitted as long as

For example, in Example 1, the eye information acquisition unit 21 having the configuration described above is used. However, the eye information acquiring unit of the present disclosure is applicable as long as it is provided in a pair corresponding to both eyes E of the subject to be examined and presents the fixation image Sf to the eye E to be examined. It is not limited to the configuration of the first embodiment.

Further, in the first embodiment, the congestion acquisition unit 27c of the control unit 27 obtains the congestion amount C at the predetermined presentation position Pp by one of the above four methods. However, as long as the congestion acquisition unit 27c (control unit 27) obtains the amount of congestion C at the predetermined presentation position Pp, the above four methods may be combined as appropriate, or other methods may be used. It is not limited to the configuration of the first embodiment.

REFERENCE SIGNS LIST 10 ophthalmologic apparatus 15 drive mechanism 21 eye information acquisition unit 27 control unit 42 visual target projection system 42a display 51 refractive member E eye to be examined Df focusing distance Pp presentation position Sb reference state Sf fixation image α rotation angle

Claims (10)

an eye information acquiring unit provided in a pair corresponding to both eyes to be examined of a subject and presenting a fixation image to at least the eyes to be examined;
a drive mechanism that adjusts the positions of the two eye information acquisition units and rotates them around the corresponding eyeball rotation point of the eye to be examined;
a control unit that controls the eye information acquisition unit and the drive mechanism,
The control unit changes the focal distance of the fixation image in the eye information acquisition unit and the rotation angle of the eye information acquisition unit while presenting the fixation image, thereby convergence and adjustment in the eye to be inspected. An ophthalmologic apparatus characterized by obtaining a relationship with. The control unit presents the fixation image in a reference state in which the focal distance and the rotation angle in the eye information acquisition unit are set in accordance with the presentation position of the fixation image, and from the reference state to the 2. The ophthalmologic apparatus according to claim 1, wherein the amount of change in the convergence is obtained until a fixation image can be properly binocularly viewed. The control unit presents the fixation image in a reference state in which the focal distance and the rotation angle in the eye information acquisition unit are set so as to match the presentation position of the fixation image on a reference plane, 2. The method of claim 1, wherein the presenting position of the fixation image is adapted from the reference plane to a displacement plane for stereoscopic viewing, and the amount of change in the adjustment when the rotation angle is changed is obtained. 3. The ophthalmic device according to 2. The eye information acquisition unit presents the fixation image displayed on the display to the eye to be inspected using a target projection system,
3. The ophthalmologic apparatus according to claim 2, wherein the control unit obtains the change amount of the convergence by changing the display position of the fixation image on the display. 3. The ophthalmologic apparatus according to claim 2, wherein the control unit obtains the change amount of the convergence by changing the rotation angle. 3. The ophthalmologic apparatus according to claim 2, wherein the control unit obtains the amount of change in convergence by changing the amount of refraction in a refraction member that refracts the axis of the eye information acquiring unit. 3. The ophthalmologic apparatus according to claim 2, wherein the control unit obtains the change amount of the convergence from the line-of-sight direction of the subject's eye when the fixation image is presented in the reference state. The control unit, based on the amount of change in the convergence when the presentation position of the fixation image is set to the far side and the amount of change in the convergence when the presentation position is set to the near side, determines the AC/A ratio 7. The ophthalmic apparatus according to any one of claims 1 to 6, characterized in that it determines the . The control unit controls the determined amount of change in adjustment, the amount of change in convergence when the presentation position of the fixation image is on the reference plane, and the amount of change in convergence when the presentation position is on the displacement plane. 4. The ophthalmologic apparatus according to claim 3, wherein the CA/C ratio is obtained based on the change amount of the convergence when the rotation angle is changed. The control unit presents the fixation image in a reference state in which the focal distance and the rotation angle in the eye information acquisition unit are set in accordance with the presentation position of the fixation image, and presents the fixation image from the reference state. 2. The ophthalmologic apparatus according to claim 1, wherein the presenting position of the fixation image is changed to near by changing the rotation angle.

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