JP6736356B2 - Ophthalmic equipment - Google Patents

Description

This invention relates to ophthalmic devices.

2. Description of the Related Art As an ophthalmologic apparatus, one capable of measuring the eye refractive power of an eye to be examined is known. Such an ophthalmologic apparatus projects a ring-shaped pattern on the fundus by irradiating the subject's eye with a ring-shaped light flux, extracts reflected light from the fundus from the center of the pupil, and obtains the size of the acquired fundus ring image. The eye refractive power value is calculated from the degree of the sheath deformation. Further, there is also an ophthalmologic apparatus in which a thin light beam is incident from the center of the pupil toward the fundus, the reflected light from the fundus is extracted from the annular zone of the pupil, and the eye refractive power value is calculated from the acquired ring-shaped pattern. In any of the ophthalmologic apparatuses, a pattern in which bright spots are arranged in a ring shape or a pattern in which multiple ring patterns are concentrically arranged may be used (Patent Documents 1 and 2). When the eye refractive power of the subject's eye is measured using such a ring-shaped pattern, a range that cannot be measured occurs, or an averaged measurement value is obtained on the pattern, so partial eye refraction It is difficult to measure changes in force values.

On the other hand, there is known an ophthalmologic apparatus capable of acquiring the distribution of the refractive power on the pupil by measuring the wavefront aberration of the return light from the subject's eye.

JP, 2012-075646, A JP, 2014-151024, A

However, the ophthalmologic apparatus capable of measuring the wavefront aberration obtains the eye refractive power value by approximating the Zernike polynomial and calculating the distribution of the wavefront aberration. The eye refractive power value obtained using the Zernike polynomial is a value obtained by approximating the entire measurement region to one curved surface. When there is a region where the refractive power changes abnormally, such as a keratoconus, most images are often perceived by a light beam passing through a predetermined region. Nevertheless, because it was unclear which region the subject perceived by the light flux passing through, the eye refractive power value obtained was used as the prescription value for the subject, and the reliability of the prescription value decreased. It was one of the factors that lead to.

The present invention has been made to solve the above problems, and provides an ophthalmologic apparatus capable of obtaining a highly reliable prescription value even when a subject has a refractive error site. The purpose is to

The ophthalmologic apparatus according to the embodiment includes a measurement optical system, a fixation optical system, a moving mechanism, a control unit, a setting unit, a calculation unit, and a selection unit. The measurement optical system projects the measurement light onto the fundus of the eye to be inspected, generates a plurality of focused lights from the return light of the measurement light from the fundus, and receives the generated plurality of focused lights to detect a point image group. .. The fixation optical system presents a fixation target to the eye to be examined. The moving mechanism moves the fixation target in the perspective direction. The control unit causes the measurement optical system to detect the point image group at each of the plurality of positions in the perspective direction by cooperatively controlling the moving mechanism and the measurement optical system. The setting unit sets two or more partial point image groups from each of the plurality of point image groups acquired by the coordinated control. The calculation unit obtains an eye refractive power value based on each partial point image group set by the setting unit. The selection unit selects one of the two or more partial point image groups based on the change of the eye refractive power value for each partial point image group in the perspective direction. The calculation unit obtains an eye refractive power value based on the partial point image group selected by the selection unit.

According to the ophthalmologic apparatus of the present invention, it is possible to obtain a highly reliable prescription value even when a refractive error portion exists in the eye to be examined.

It is a schematic diagram showing an example of composition of an optical system of an ophthalmologic apparatus concerning an embodiment. It is a schematic diagram showing an example of composition of a Hartmann board concerning an embodiment. It is a schematic diagram showing another example of composition of a Hartmann board concerning an embodiment. It is explanatory drawing which represents typically the relationship between the Hartmann board and the area sensor which concern on embodiment. It is a schematic diagram showing an example of composition of a processing system of an ophthalmologic apparatus concerning an embodiment. It is a schematic diagram showing an example of composition of a processing system of an ophthalmologic apparatus concerning an embodiment. FIG. 6 is an operation explanatory diagram of the eye refractive power value calculation unit according to the embodiment. FIG. 6 is an operation explanatory diagram of the eye refractive power value calculation unit according to the embodiment. FIG. 6 is an operation explanatory diagram of the eye refractive power value calculation unit according to the embodiment. It is explanatory drawing in the case where a pupil has a refractive error part. It is operation|movement explanatory drawing of the ophthalmologic apparatus which concerns on embodiment. It is operation|movement explanatory drawing of the ophthalmologic apparatus which concerns on embodiment. It is a flowchart of the operation example of the ophthalmologic apparatus which concerns on embodiment. It is a flowchart of the operation example of the ophthalmologic apparatus which concerns on embodiment.

An example of an embodiment of an ophthalmologic apparatus according to the present invention will be described in detail with reference to the drawings. It should be noted that the contents of the documents cited in this specification and any known techniques can be applied to the following embodiments.

<Ophthalmologic equipment>
The ophthalmologic apparatus according to the embodiment can perform at least one of an arbitrary subjective test and an arbitrary objective measurement. In the subjective test, information (eg, optotype) is presented to the subject, and the result is acquired based on the response of the subject to the information. The subjective test includes subjective refraction measurement such as distance test, near test, contrast test, and glare test, and visual field test. In the objective measurement, the eye to be inspected is irradiated with light, and information on the eye to be inspected is acquired based on the detection result of the return light. The objective measurement includes measurement for acquiring the characteristic of the eye to be inspected and photographing for acquiring the image of the eye to be inspected. For objective measurement, objective refraction measurement, corneal shape measurement, intraocular pressure measurement, fundus photography, tomographic imaging (OCT imaging) using optical coherence tomography (OCT), and OCT were used. There are measurements etc.

Hereinafter, the ophthalmologic apparatus according to the embodiment is capable of performing a distance test, a near test, etc. as a subjective test, and as an objective measurement, an objective refraction measurement by a wavefront aberration measurement, a corneal shape measurement, etc. It shall be a possible device. However, the configuration of the ophthalmologic apparatus according to the embodiment is not limited to this.

[Constitution]
The ophthalmologic apparatus according to the embodiment includes a face receiving portion fixed to a base, and a gantry that can move in the front, rear, up, down, left and right with respect to the base. The gantry is provided with a head unit in which an optical system for performing inspection (measurement) of the eye to be inspected is housed. By operating the operation unit arranged at the position on the examiner side, the face receiving unit and the head unit can be moved relative to each other. Further, the ophthalmologic apparatus can automatically move the face receiving section and the head section relatively by executing the alignment described later.

FIG. 1 shows a configuration example of an optical system of the ophthalmologic apparatus according to the embodiment. The ophthalmologic apparatus includes a Z alignment system 1, an XY alignment system 2, a kerato measurement system 3, an optotype projection system 4, an observation system 5, an aberration measurement projection system 6, and an aberration as an optical system for inspecting the eye E to be inspected. A measurement light receiving system 7 is included. The ophthalmologic apparatus also includes a processing unit 9.

(Processing unit 9)
The processing unit 9 controls each unit of the ophthalmologic apparatus. In addition, the processing unit 9 can execute various arithmetic processes. The processing unit 9 includes a processor. The function of the processor is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, SPLD (Simple Programmable Logic), or a programmable logic device (SPLD). , FPGA (Field Programmable Gate Array) and the like. The processing unit 9 realizes the function according to the embodiment by reading and executing a program stored in a storage circuit or a storage device, for example.

(Observation system 5)
The observation system 5 captures a moving image of the anterior segment of the eye E to be examined. Light (infrared light) from the anterior segment of the eye E to be examined passes through the objective lens 51, the dichroic mirror 52, and the aperture of the diaphragm 53. The light that has passed through the aperture of the diaphragm 53 passes through the half mirror 22, passes through the relay lens 54, and is guided to the imaging lens 55. The image forming lens 55 forms an image of the light guided from the relay lens 54 on the light receiving surface of the area sensor 56. The light receiving surface of the area sensor 56 is arranged at a position that is substantially conjugate with the pupil of the eye E to be inspected. The area sensor 56 performs imaging and signal output at a predetermined rate. The output (video signal) of the area sensor 56 is input to the processing unit 9. The processing unit 9 displays the anterior segment image E′ based on this video signal on the display screen 10 a of the display unit 10. The anterior segment image E′ is, for example, an infrared moving image. The observation system 5 may include an illumination light source for illuminating the anterior segment.

(Z alignment system 1)
The Z alignment system 1 irradiates the eye E with light (infrared light) for performing alignment in the optical axis direction (front-back direction, Z direction) of the observation system 5. The light output from the Z alignment light source 11 is applied to the cornea K of the eye E to be examined, reflected by the cornea K, and guided to the imaging lens 12. The imaging lens 12 images the guided light on the light receiving surface of the line sensor 13. When the position of the apex of the cornea changes in the front-back direction, the projection position of light on the line sensor 13 changes. The output of the line sensor 13 is input to the processing unit 9. The processing unit 9 obtains the position of the apex of the cornea of the eye E based on the projection position of the light on the line sensor 13, and executes Z alignment based on this.

(XY alignment system 2)
The XY alignment system 2 irradiates the eye E with light (infrared light) for performing alignment in a direction (horizontal direction (X direction), vertical direction (Y direction)) orthogonal to the optical axis of the observation system 5. .. The XY alignment system 2 includes an XY alignment light source 21 provided on the optical path branched from the observation system 5 by the half mirror 22. The light output from the XY alignment light source 21 passes through the relay lens 23 and is reflected by the half mirror 22. The light reflected by the half mirror 22 is condensed at the front focus position of the objective lens 51 on the optical axis of the observation system 5, then passes through the dichroic mirror 52, becomes parallel light by the objective lens 51, and is examined. The cornea K of E is irradiated. The light reflected on the surface of the cornea K forms a Purkinje image in the vicinity of the reflection focal point position on the cornea surface of the eye E to be examined. The XY alignment light source 21 is arranged at a position that is substantially optically conjugate with the focal position of the objective lens 51. The light reflected by the cornea K is guided to the area sensor 56 through the observation system 5. An image Br, which is a Purkinje image (bright spot) of the light output from the XY alignment light source 21, is formed on the light receiving surface of the area sensor 56.

As shown in FIG. 1, the processing unit 9 displays the anterior segment image E′ including the bright spot image Br and the alignment mark AL on the display screen 10a. When performing the XY alignment manually, the examiner performs a movement operation of the optical system so as to guide the bright spot image Br into the alignment mark AL. When performing the alignment automatically, the processing unit 9 controls the mechanism for moving the optical system so that the displacement of the bright spot image Br with respect to the alignment mark AL is canceled.

(Kerato measurement system 3)
The kerato measurement system 3 projects a ring-shaped light flux (infrared light) for measuring the curvature of the cornea K onto the cornea K. The kerato plate 31 is arranged near the objective lens 51. A kerat ring light source 32 is provided on the back side (objective lens 51 side) of the kerato plate 31. By illuminating the kerato plate 31 with the light from the kerat ring light source 32, a ring-shaped light beam is projected on the cornea K. The reflected light (keratoling image) is detected by the area sensor 56 together with the anterior segment image. The processing unit 9 calculates a corneal curvature parameter by performing a known calculation based on this keratling image. Instead of the kerat ring, a Placido ring plate composed of multiple rings may be arranged. In this case, not only the curvature of the cornea but also the corneal shape can be measured.

(Target projection system 4)
The optotype projection system 4 presents various optotypes such as a fixation target and an optotype for a subjective test to the eye E. The optotype chart 42 is controlled by the processing unit 9 and displays a pattern representing the optotype. The light (visible light) output from the light source 41 passes through the target chart 42, the relay lens 43 and the field lens 44, is reflected by the reflection mirror 45, is transmitted through the dichroic mirror 68, and is transmitted by the dichroic mirror 52. Is reflected. The light reflected by the dichroic mirror 52 passes through the objective lens 51 and is projected onto the fundus Ef.

The moving unit 46 including the light source 41 and the target chart 42 is movable along the optical axis of the target projection system 4. The position of the moving unit 46 is adjusted so that the optotype chart 42 and the fundus oculi Ef are optically substantially conjugate.

The optotype chart 42 can be controlled by the processing unit 9 to display a pattern representing a fixation target for fixing the eye E to be inspected. By sequentially changing the display position of the pattern representing the fixation target on the optotype chart 42, the fixation position can be moved to guide the line of sight or the adjustment of the eye to be inspected. In such an optotype chart 42, one of a plurality of optotypes drawn on a liquid crystal panel, an electronic display device using EL (electroluminescence), or a rotating glass plate is appropriately placed on the optical axis. There is something to place (turret type). The optotype projection system 4 may also include a glare inspection optical system for projecting glare light onto the eye E along with the above-described optotype.

When performing the subjective test, the processing unit 9 controls the mobile unit 46 based on the result of the objective measurement. The processing unit 9 causes the optotype selected by the examiner or the processing unit 9 to be displayed on the optotype chart 42. As a result, the target is presented to the subject. The subject responds to the optotype. Upon receiving the input of the response content, the processing unit 9 performs further control and calculation of the subjective test value. For example, in the visual acuity measurement, the processing unit 9 selects and presents the next target based on the response to the Landolt ring and the like, and repeats this to determine the visual acuity value.

In objective measurement (objective refraction measurement, etc.), a landscape chart is projected on the fundus Ef. Alignment is performed while the subject is fixated on the landscape chart, and the eye refractive power is measured in the clouded state.

(Aberration measuring projection system 6 and aberration measuring light receiving system 7)
The aberration measurement projection system 6 and the aberration measurement light receiving system 7 are used to measure the eye aberration characteristics of the eye E to be inspected. The aberration measurement projection system 6 projects a light beam (infrared light) for measuring the eyeball aberration characteristic onto the fundus Ef. The aberration measurement light receiving system 7 receives the return light of this light flux from the fundus Ef of the eye E to be examined. The eye aberration characteristic of the eye E to be inspected is obtained from the result of the return light received by the aberration measurement light receiving system 7.

As the light source (point light source) 61, a light source that emits light having a wavelength in the vicinity of 850 nm is used. Examples of the light source 61 include a Super Luminescent Diode (SLD), but may be an LD (laser diode) or an LED with a small emission diameter. The moving unit 69 including the light source 61 is movable along the optical axis of the aberration measurement projection system 6. The light source 61 is arranged at a position that is substantially conjugate with the fundus oculi Ef. The light (measurement light) output from the light source 61 passes through the relay lens 62 and the field lens 63 and then through the polarizing plate 64. The polarizing plate 64 transmits only the p-polarized component of the polarized components of the light output from the light source 61. The light transmitted through the polarizing plate 64 passes through the aperture of the diaphragm 65, is reflected by the polarization beam splitter 66 that reflects the p-polarized component, passes through the rotary prism 67, and is reflected by the dichroic mirror 68. The light reflected by the dichroic mirror 68 is reflected by the dichroic mirror 52, passes through the objective lens 51, and is projected onto the fundus oculi Ef.

The light source may not be directly arranged at the position of the light source 61, but the light from the light source 61 may be guided to the relay lens 62 by an optical fiber connecting the light source device and the ophthalmologic apparatus. In this case, the fiber end of the optical fiber is arranged at a position that is substantially conjugate with the fundus oculi Ef.

The rotary prism 67 is used for averaging the unevenness of the reflectance in the blood vessels of the fundus Ef and the diseased part, and for reducing the speckle noise due to the SLD light source.

The light incident on the eye E is not maintained in the polarization state due to the scattering reflection by the fundus, and the return light from the fundus Ef is the light in which the p-polarized component and the s-polarized component are mixed. The return light from the fundus Ef passes through the objective lens 51 and is reflected by the dichroic mirrors 52 and 68. The return light reflected by the dichroic mirror 68 passes through the rotary prism 67 and is guided to the polarization beam splitter 66. The polarization beam splitter 66 transmits only the s-polarized component of the polarized component of the return light. The light of the s-polarized component that has passed through the polarization beam splitter 66 passes through the field lens 71, is reflected by the reflection mirror 72, passes through the relay lens 73, and is guided to the moving unit 77. The light specularly reflected by the surface of the objective lens 51 and the cornea K of the eye E to be inspected is reflected by the polarization beam splitter 66 because it maintains p-polarized light and does not enter the wavefront aberration measurement system 7, so that the occurrence of ghost can be reduced.

The moving unit 77 includes a collimator lens 74, a Hartmann plate 75, and an area sensor 76. As the area sensor 76, for example, a CCD (Charge Coupled Device) image sensor or a CMOS (Complementary Metal Oxide Semiconductor) image sensor is used. The light guided to the moving unit 77 passes through the collimator lens 74 and enters the Hartmann plate 75. The Hartmann plate 75 is arranged at a position which is substantially conjugate with the pupil of the eye E to be inspected. The moving unit 77 is movable along the optical axis of the aberration measurement light receiving system 7. The moving unit 77 is moved along the optical axis according to the eye refractive power value of the eye E to be inspected so that the fundus Ef and the front focus position of the collimator lens 74 are substantially optically conjugate.

2A and 2B are explanatory views of the Hartmann plate 75 according to the embodiment. 2A and 2B schematically show the configuration of the Hartmann plate 75 when viewed from the optical axis direction of the aberration measurement light receiving system 7. The Hartmann plate 75 generates a plurality of focused lights from the returned light from the fundus Ef. As shown in FIGS. 2A and 2B, a plurality of microlenses 75A are arranged in a lattice on the Hartmann plate 75. The Hartmann plate 75 divides the incident light into a large number of luminous fluxes and collects them. For example, the Hartmann plate 75 has a configuration in which a plurality of microlenses 75A are arranged on a glass plate by etching, molding or the like, as shown in FIG. 2A. In this case, the aperture of each microlens can be made large, and the signal strength can be increased. Further, as shown in FIG. 2B, the Hartmann plate 75 has a structure in which a plurality of microlenses 75A are arranged by providing a light-shielding portion 75B by forming a chrome light-shielding film or the like around each microlens 75A. May be. The microlenses 75A are not limited to those arranged in a square arrangement, but may be arranged on a concentric circle, arranged at each vertex of a triangle, or arranged in hexagonal close packing.

The area sensor 76 is arranged at the focal position of the microlens 75A and detects the light (focused light) condensed by the Hartmann plate 75, respectively. As shown in FIG. 3, the light receiving surface of the area sensor 76 corresponds to the light irradiation areas a ₁ ,..., B ₁ ,..., C ₁ ,... On the pupil Ep of the eye E to be examined. Then, the point images A ₁ ,..., B ₁ ,..., C ₁ ,... Are formed by the microlenses 75A of the Hartmann plate 75. When the fundus oculi Ef and the front focus position of the collimator lens 74 are in an optically substantially conjugate relationship as described above, the distance between the barycentric positions of the point images formed on the light receiving surface of the area sensor 76 is the lens of the microlens 75A. It is almost equal to the center distance. The area sensor 76 detects a point image group formed by the microlenses 75A of the Hartmann plate 75. The processing unit 9 acquires the detection signal based on the point image group detected by the area sensor 76 and the position information indicating the detection position of the point image group, and analyzes the position of the point image formed by each microlens 75A. Thus, the wavefront aberration of the light incident on the Hartmann plate 75 is obtained. Thereby, the eye aberration characteristic of the eye E to be examined is obtained. The processing unit 9 obtains an eye refractive power value of the eye E from the obtained eye aberration characteristic.

Based on the calculated eye refractive power value, the processing unit 9 sets the moving unit 69 and the moving unit 77 so that the light source 61, the fundus oculi Ef, and the front focus position of the collimator lens 74 are optically conjugated. It can be moved in the optical axis direction. Further, the processing unit 9 can move the moving unit 46 in the optical axis direction in association with the movement of the moving units 69 and 77.

(Configuration of processing system)
A processing system of the ophthalmologic apparatus according to the embodiment will be described. An example of the functional configuration of the processing system of the ophthalmologic apparatus is shown in FIGS. 4 and 5. FIG. 4 shows an example of a functional block diagram of a processing system of the ophthalmologic apparatus according to the embodiment. FIG. 5 shows an example of a functional block diagram of the arithmetic processing unit 120 of FIG. The processing unit 9 includes a control unit 110 and an arithmetic processing unit 120. Further, the ophthalmologic apparatus according to the embodiment includes the display unit 170, the operation unit 180, the communication unit 190, and the moving mechanism 200.

The moving mechanism 200 accommodates optical systems such as a Z alignment system 1, an XY alignment system 2, a kerato measurement system 3, a target projection system 4, an observation system 5, an aberration measurement projection system 6, and an aberration measurement light receiving system 7. It is a mechanism for moving the head part in the front, rear, up, down, left and right directions. For example, the moving mechanism 200 is provided with an actuator that generates a driving force for moving the moving mechanism 200 and a transmission mechanism that transmits the driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is composed of, for example, a combination of gears and a rack and pinion. The controller 110 (main controller 111) controls the moving mechanism 200 by sending a control signal to the actuator.

(Control unit 110)
The control unit 110 includes a processor and controls each unit of the ophthalmologic apparatus. The control unit 110 includes a main control unit 111 and a storage unit 112. A computer program for controlling the ophthalmologic apparatus is stored in the storage unit 112 in advance. The computer program includes a light source control program, a sensor control program, an optical system control program, an arithmetic processing program, a user interface program, and the like. When the main control unit 111 operates according to such a computer program, the control unit 110 executes control processing.

The main control unit 111 performs various controls of the ophthalmologic apparatus as a measurement control unit. Controlling the Z alignment system 1 includes control of the Z alignment light source 11 and control of the line sensor 13. Control of the Z alignment light source 11 includes turning on and off the light source, adjusting the light amount, and the like. The control of the line sensor 13 includes exposure adjustment of the detection element, gain adjustment, detection rate adjustment, and the like. As a result, the Z alignment light source 11 is switched on and off, or the light amount is changed. The main control unit 111 captures the signal detected by the line sensor 13 and specifies the projection position of light on the line sensor 13 based on the captured signal. The main control unit 111 obtains the position of the apex of the cornea of the eye E based on the identified projection position, and controls the moving mechanism 200 based on this to move the head unit in the front-back direction (Z alignment).

Control of the XY alignment system 2 includes control of the XY alignment light source 21. The control of the XY alignment light source 21 includes turning on and off the light source, adjusting the light amount, and the like. As a result, lighting and non-lighting of the XY alignment light source 21 are switched, and the amount of light is changed. The main control unit 111 captures the signal detected by the area sensor 56 and identifies the position of the bright spot image based on the return light of the light from the XY alignment light source 21 based on the captured signal. The main control unit 111 controls the moving mechanism 200 to move the head unit in the left-right and up-down directions so that the displacement from the position of the bright spot image with respect to a predetermined target position (for example, the center position of the alignment mark) is canceled. (XY alignment).

The control for the kerato measurement system 3 includes control of the kerat ring light source 32. The control of the keratling light source 32 includes turning on and off the light source and adjusting the light amount. Thereby, lighting and non-lighting of the keratling light source 32 are switched, and the light amount is changed. The main control unit 111 causes the arithmetic processing unit 120 to perform a known arithmetic operation on the keratling image detected by the area sensor 56. Thereby, the corneal shape parameter of the eye E to be examined is obtained.

The control of the target projection system 4 includes control of the light source 41, control of the target chart 42, and movement control of the moving unit 46. The control of the light source 41 includes turning on/off the light source and adjusting the light amount. Thereby, lighting and non-lighting of the light source 41 are switched, or the amount of light is changed. The control of the optotype chart 42 includes turning on and off the display of the optotypes and the fixation target and switching the display position of the fixation target. Thereby, the optotype or the fixation target is projected on the fundus Ef of the eye E to be examined. For example, the ophthalmologic apparatus is provided with a moving mechanism 46A that moves the moving unit 46 in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism 46A is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 111 controls the moving mechanism 46A by sending a control signal to the actuator to move the moving unit 46 in the optical axis direction. Thereby, the position of the moving unit 46 is adjusted such that the optotype chart 42 and the fundus oculi Ef are optically conjugated.

Control of the observation system 5 includes control of the area sensor 56, turning on and off of an anterior segment illumination LED (not shown), light amount adjustment, and the like. The control of the area sensor 56 includes exposure adjustment, gain adjustment, detection rate adjustment, and the like of the area sensor 56. The main control unit 111 captures the signal detected by the area sensor 56, and causes the arithmetic processing unit 120 to perform processing such as image formation based on the captured signal. When the observation system 5 includes an illumination light source, the main control unit 111 can control the illumination light source.

Controlling the aberration measurement projection system 6 includes control of the light source 61, control of the rotary prism 67, control of the moving unit 69, and the like. The control of the light source 61 includes turning on/off the light source and adjusting the light amount. Thereby, lighting and non-lighting of the light source 61 are switched, or the light amount is changed. The control of the rotary prism 67 includes rotation control of the rotary prism 67. For example, a rotation mechanism that rotates the rotary prism 67 is provided, and the main control unit 111 rotates the rotary prism 67 by controlling this rotation mechanism. For example, the ophthalmologic apparatus is provided with a moving mechanism 69A that moves the moving unit 69 in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism 69A is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main controller 111 controls the moving mechanism 69A by sending a control signal to the actuator to move the moving unit 69 in the optical axis direction.

The control of the aberration measurement light receiving system 7 includes control of the area sensor 76, movement control of the moving unit 77, and the like. The control of the area sensor 76 includes exposure adjustment, gain adjustment, detection rate adjustment, and the like of the area sensor 76. The main control unit 111 takes in the signal detected by the area sensor 76, and causes the arithmetic processing unit 120 to perform calculation processing of eye aberration characteristics based on the taken-in signal. For example, the ophthalmologic apparatus is provided with a moving mechanism 77A that moves the moving unit 77 in the optical axis direction. Similar to the moving mechanism 200, the moving mechanism 77A is provided with an actuator that generates a driving force for moving the moving mechanism and a transmission mechanism that transmits the driving force. The main control unit 111 controls the moving mechanism 77A by sending a control signal to the actuator to move the moving unit 77 in the optical axis direction.

The main control unit 111 can display various information on the display unit 170 as a display control unit. The information displayed on the display unit 170 includes an objective measurement result (aberration measurement result) obtained by using the above optical system, a subjective test result, and an image and information based on these. For example, the display unit 170 displays the eye refractive power value calculated by the arithmetic processing unit 120, the information indicating the distribution of the eye refractive power value generated by the distribution information generation unit 124 as described later, and the like. The main control unit 111 can superimpose these pieces of information on each other and display the information on the display unit 170, or display a part of the information.

Further, the main control unit 111 performs a process of writing data in the storage unit 112 and a process of reading data from the storage unit 112.

(Storage unit 112)
The storage unit 112 stores various data. The data stored in the storage unit 112 includes, for example, the test result of the subjective test, the measurement result of the objective measurement, the image data of the anterior ocular segment image, the image data of the Hartmann point image, and the eye information. The eye information includes information about the subject such as a patient ID and name, and information about the eye such as left/right eye identification information. The storage unit 112 also stores various programs and data for operating the ophthalmologic apparatus.

(Arithmetic processing unit 120)
The arithmetic processing unit 120 includes a processor, and executes the processes of the following units according to a computer program stored in a storage unit (or storage unit 112) not shown. The arithmetic processing unit 120 includes a setting unit 121, an eye refractive power value calculation unit 122, a selection unit 123, and a distribution information generation unit 124.

The setting unit 121 sets one or more partial point image groups from the point image group detected by the area sensor 76. The partial point image group includes at least three point images. The setting unit 121 can set one or more partial point image groups based on the distribution of the point image groups detected by the area sensor 76. For example, the setting unit 121 sets the partial point image group so as to include three or more point images having a predetermined positional relationship. Examples of three or more point images having a predetermined positional relationship are three or more point images adjacent to each other, three or more point images included in a region having a predetermined shape, a predetermined part of the pupil (for example, the center of the pupil). There are three or more point images included in the area including the position (position on the area sensor 76) corresponding to. The setting unit 121 can set the partial point image group such that at least a part of the area defined by the one partial point image group overlaps the area defined by the other one partial point image group. is there.

The setting unit 121 can also set the partial point image group so as to include the point images designated by the user such as the examiner on the operation unit 180. For example, the setting unit 121 sets the partial point image group so that the anterior ocular segment image displayed on the display unit 170 includes the point image on the area sensor 76 corresponding to the region designated by the user.

The eye refractive power value calculation unit 122 obtains a single eye refractive power value by analyzing the point image group detected by the area sensor 76. For example, the eye refractive power value calculation unit 122 analyzes the point image group formed on the light receiving surface of the area sensor 76 by the Hartmann plate 75 in the aberration measurement light receiving system 7. Specifically, the eye-refractive-power value calculation unit 122 obtains the inclination of the light ray specified from the image in which the obtained point image group is drawn. The eye-refractive-power value calculation unit 122 calculates an approximate expression of the wavefront by a known calculation using the calculated inclination amount of the light beam. The obtained approximate expression of the wavefront is represented by a Zernike coefficient and a Zernike polynomial. The wavefront aberration is represented by the Zernike coefficient. The eye-refractive-power value calculation unit 122 obtains the spherical power S, the astigmatic power C, and the astigmatic axis angle A as the eye-refractive-power value from the low-order term of the Zernike coefficient by known calculation.

Further, the eye-refractive-power value calculation unit 122 can obtain the eye-refractive-power calculation value for each of the partial point image groups set by the setting unit 121. That is, the eye-refractive-power value calculation unit 122 calculates one or more eye-refractive-power values based on one or more partial point image groups set by the setting unit 121 among the point image groups detected by the area sensor 76.

Hereinafter, an example of calculation processing of the eye refractive power value by the eye refractive power value calculation unit 122 will be described.

6 to 8 are explanatory views of a processing example of the eye refractive power value calculation unit 122. FIG. 6 is an explanatory diagram for obtaining the spherical power S of the eye to be inspected based on any two point images included in the partial point image group set by the setting unit 121. FIG. 6 schematically shows a sectional structure taken along a sectional line passing through the two microlenses 75A forming the above-mentioned two point images. FIG. 7 is a perspective view schematically showing an intersection of a straight line connecting the micro lens 75A of the Hartmann plate 75 and the area sensor 76 when the eye refractive power value of the eye to be inspected includes only the spherical power. FIG. 7 is a perspective view in which the Hartmann plate 75, the area sensor 76, and the virtual plane 80 of the light source are arranged in the optical axis direction of the aberration measurement light receiving system 7. FIG. 8 is a perspective view schematically showing an intersection of a straight line connecting the microlens 75A of the Hartmann plate 75 and the area sensor 76 when the eye refractive power value of the eye to be inspected includes the astigmatic power. FIG. 8 is a perspective view in which the Hartmann plate 75, the area sensor 76, and the virtual plane 81 at the intersection are arranged in the optical axis direction of the aberration measurement light receiving system 7. Note that FIG. 8 illustrates an explanatory diagram in the case of unilateral astigmatism for convenience of description.

Assuming that the distance from the Hartmann plate 75 to the virtual intersection of the rays is F and the magnification from the pupil of the eye E to the Hartmann plate 75 is M, the eye refractive power value calculation unit 122 calculates the following formula (1). ), the spherical power S of the eye E can be obtained.

When the eye refractive power value of the eye E includes only the spherical power, as shown in FIG. 7, a straight line connecting the lens center of the microlens 75A of the Hartmann plate 75 and the barycentric position of the point image on the light receiving surface of the area sensor 76. Intersect at one point. Therefore, for any two arbitrary point images, the intersection of two straight lines connecting the lens center of the microlens 75A and the barycentric position of the point image can be specified as the focus position of the eye E to be examined.

As shown in FIG. 6, when the distance between the lens centers of the two microlenses 75A is L and the distance from the Hartmann plate 75 to the area sensor 76 is f, the eye refractive power value calculation unit 122 calculates the following formula (2 ), the distance F from the Hartmann plate 75 to the intersection can be obtained.

In Expression (2), the displacement amount dx represents the displacement amount between the lens center of the microlens 75A and the position of the center of gravity of the point image on the corresponding area sensor 76 (see FIG. 6). The displacement amount is represented by the following equation (3) as shown in FIG.

The distance L and the distance f are known information by optical design, and the distance h is information that can be specified by the detection result obtained by the area sensor 76. From the above, the eye-refractive-power value calculation unit 122 can calculate the spherical power S of the eye E as described above.

On the other hand, when the eye refractive power value of the eye E includes the astigmatic power, the point image formed on the area sensor 76 by the light passing through the microlens 75A of the Hartmann plate 75 has a power in the meridian direction of astigmatism. It receives and moves (see FIG. 8). On the virtual plane 81 at the first focus position (rear focus position) of the eye E to be examined, point images are arranged in the meridian direction of astigmatism, and the virtual plane at the second focus position (front focus position) of the eye E to be examined. Point images are arranged in the astigmatic meridian direction orthogonal to the meridian direction. Therefore, the eye-refractive-power value calculation unit 122 specifies the position where at least three point images are aligned on a straight line as the focus position (back-side focus position, front-side focus position) of the eye E to be examined, and based on the specified focus position. The eye refractive power value of the eye E can be obtained from the focal length. The eye-refractive-power value calculation unit 122 may specify a position where it is determined that at least three point images are lined up on a straight line within a predetermined error range, as the focus position of the eye E to be inspected.

For example, if the distance from the Hartmann plate 75 to the back focal position of the subject's eye E is F and the distance from the Hartmann plate 75 to the front focal position of the subject's eye E is F', then the eye refractive power value calculation unit 122 The spherical power D is calculated from the distance F, and the spherical power D′ is calculated from the distance F′. When the spherical power S is D, the eye-refractive-power value calculation unit 122 obtains the astigmatic power C by calculating (D′−D), and then on the plane 81 at the back focal position of the specified eye E to be examined. The inclination θ of the straight line where the three point images are lined up can be obtained as the astigmatic axis angle A. Alternatively, when the spherical power S is D′, the eye refractive power value calculation unit 122 calculates the astigmatic power C by calculating (D−D′), and the plane at the front focus position of the specified eye E to be examined. The inclination θ′ of the straight line in which the three point images are arranged can be obtained as the astigmatic axis angle A.

The eye-refractive-power value calculation unit 122 obtains a representative value by averaging two or more eye-refractive-power values obtained for one partial point image group, or obtains a representative value by performing different weighted addition for each part. It is possible to Further, the eye-refractive-power value calculation unit 122 obtains two or more eye-refractive-power values based on the two or more partial point image groups, and obtains a representative value obtained by averaging the obtained two or more eye-refractive-power values. Is possible. For example, the eye-refractive-power value calculating unit 122 may obtain a representative value obtained by averaging two or more eye-refractive-power values excluding a predetermined area (for example, an area where the degree of blurring is significant due to cataract or the like). Further, the eye-refractive-power value calculation unit 122 can obtain a representative value by performing different weighted addition for each site. For example, the eye-refractive-power value calculation unit 122 may obtain the representative value by weighted addition corresponding to the distance from the center position (centroid position) of the partial point image group.

6 to 8, the example in which the eye refractive power value is calculated mainly based on the two or at least three point images of the partial point image group has been described, but the process of the eye refractive power value calculation unit 122 is described. Is not limited to this. For example, the eye-refractive-power value calculation unit 122 calculates the eye-refractive-power values for all the point images detected by the area sensor 76, averages the calculated eye-refractive-power values, and weights and adds different values for each part. The representative value obtained by performing the above may be obtained as a single eye refractive power value.

The eye-refractive-power value calculation unit 122 performs a first process for obtaining an eye-refractive-power value for each of the partial point image groups according to the presence or absence of point images in a predetermined range in the point image group, and a single process for the point image groups. It is possible to execute any of the second processes for obtaining one eye refractive power value. For example, the eye-refractive-power value calculating unit 122 executes the first process when the point image group has a missing point image in a predetermined range, and the second process when the point image group has no missing point image in the predetermined range. Execute the process. Further, the eye-refractive-power value calculation unit 122 may execute either the first process or the second process according to the number of point images included in the point image group. In this case, the eye-refractive-power value calculation unit 122 executes the first process when the number of point images included in the point image group is less than or equal to the threshold value, and the first process when the number of point images included in the point image group is less than the threshold value. Two processes can be performed.

Further, the eye-refractive-power value calculation unit 122 obtains the eye-refractive-power value for each of the partial point image groups according to the presence or absence of a point image based on partial refractive error (refractive power change) included in the point image group. It is possible to execute either the first processing or the second processing for obtaining a single eye refractive power value for the point image group. For example, the eye-refractive-power value calculation unit 122 executes the first process when the point image group has a point image based on the partial refractive error, and when the point image group does not have the point image based on the partial refractive error. 2 Execute the process.

The eye refractive power value calculation unit 122 also calculates the corneal refractive power, the corneal astigmatism degree, and the corneal astigmatic axis angle based on the keratling image acquired by the observation system 5. For example, the eye refractive power value calculation unit 122 calculates the corneal curvature radius of the strong main meridian or the weak main meridian on the anterior surface of the cornea by analyzing the keratling image, and calculates the above parameter based on the corneal curvature radius.

The selection unit 123 selects one of the two or more partial point image groups set by the setting unit 121. The eye-refractive-power value calculation unit 122 calculates the eye-refractive-power value as a prescription value based on the partial point image group selected by the selection unit 123. The selecting unit 123 determines two or more partial points based on the change in the perspective direction of the eye refractive power value for each partial point image group obtained in the state where the fixation target is presented at each of the plurality of positions in the perspective direction. Select one of the images. Thereby, it becomes possible to select the eye refractive power value that contributes to the perception of the subject as the prescription value.

The distribution information generation unit 124 generates the distribution information of the eye refractive power values based on the positions of the two or more partial point image groups and the two or more eye refractive power values calculated by the eye refractive power value calculation unit 122. .. The main control unit 111 can display the distribution information generated by the distribution information generation unit 124 on the display unit 170. This makes it possible to easily grasp the eye refractive power value obtained for the partial point image group in association with the position of the partial point image group. At this time, the main control unit 111 may superimpose the distribution information on the pupil region depicted in the anterior segment image and display the distribution information on the display unit 170. Further, the main control unit 111 may display the partial point image group selected by the selection unit 123 on the display unit 170 in a distinguishable manner in the distribution information of the eye refractive power value.

(Display unit 170, operation unit 180)
The display unit 170 serves as a user interface unit and displays information under the control of the control unit 110 (main control unit 111). The display unit 170 includes the display unit 10 shown in FIG.

The operation unit 180 is used as a user interface unit to operate the ophthalmologic apparatus. The operation unit 180 includes various hardware keys (joystick, buttons, switches, etc.) provided in the ophthalmologic apparatus. The operation unit 180 may also include various software keys (buttons, icons, menus, etc.) displayed on the touch-panel display screen 10a.

At least a part of the display unit 170 and the operation unit 180 may be integrally configured. A typical example thereof is a touch panel type display screen 10a.

(Communication unit 190)
The communication unit 190 has a function of communicating with an external device (not shown). The communication unit 190 may be provided in the processing unit 9, for example. The communication unit 190 has a configuration according to the form of communication with an external device.

The aberration measurement projection system 6 and the aberration measurement light receiving system 7 are examples of the “measurement optical system” according to the embodiment. The target projection system 4 is an example of the “fixation optical system” according to the embodiment. The eye refractive power value calculation unit 122 is an example of a “calculation unit” according to the embodiment. The Hartmann plate 75 is an example of the “lens array” according to the embodiment.

[Operation example]
An operation example of the ophthalmologic apparatus according to this embodiment will be described.

The eye E to be inspected may have a plurality of regions having different refractive powers on the pupil, for example. For example, when the eye E to be inspected is a keratoconus eye, there are a region having a small corneal curvature due to the protrusion of the central portion and a region other than that, and therefore there are a plurality of regions having different refractive powers on the pupil.

FIG. 9 schematically shows an example of a point image group detected by the area sensor 76 when the eye E to be inspected is a keratoconus eye. In this case, since the region R having a small corneal curvature is a region corresponding to the refractive error region, the area sensor 76 detects a point image as shown in FIG. 9, and the area corresponding to the region R has a distribution density of point images. A region with low (or a region with high distribution density) occurs. In the case of the eye to be inspected in which a plurality of regions having different refractive powers are present, the subject often perceives most of the image based on the light flux passing through the predetermined region. As shown in FIG. 9, when a region R having different refracting powers and other regions exist on the pupil Ep, the interval between the point images detected by the area sensor 76 is the region R and the other regions. Different. Therefore, although it is possible to determine that diplopia occurs in the subject's eye, it is not known which region the subject preferentially perceives the image by the light flux passing through, so what kind of prescription value should be given to the subject? I didn't know what to present.

On the other hand, according to the embodiment, the eye refractive power value is obtained for each of the two or more partial point image groups set from the obtained point images, and it contributes to the perception of the two or more partial point image groups. The eye refractive power value of the partial point image group can be obtained as a prescription value.

For example, the main control unit 111, as a measurement control unit, controls the moving mechanism 46A and the target projection system 4 in a coordinated manner, so that the aberration is generated in a state where the fixation target is presented at each of a plurality of positions in the perspective direction. The measurement projection system 6 and the aberration measurement light receiving system 7 are caused to detect a point image group. As shown in FIG. 10, the setting unit 121 sets partial point image groups R1′ and R2′ corresponding to the regions R1 and R2 in the pupil Ep. The eye-refractive-power value calculation unit 122 obtains the eye-refractive-power value based on each partial point image group set by the setting unit 121. Thereby, as shown in FIG. 10, change characteristics T1 and T2 of the eye refractive power value corresponding to the optotype presenting positions are obtained for the regions R1 and R2, respectively.

When the target is presented at a position corresponding to a predetermined eye refractive power value, the selection unit 123 determines which partial point image group has the eye refractive power value, thereby making it possible for the subject's perception. Select the partial point image group that contributed. Specifically, the change characteristic T0 of the eye refractive power value corresponding to the optotype presenting position is uniquely determined. The selecting unit 123 uses the partial point image group (region R1 in FIG. 11) having the variation characteristic (variation characteristic T1 in FIG. 11) that minimizes the error with respect to the variation characteristic T0, mainly for the subject to perceive. It is possible to presume that there is a region and select that region. The eye-refractive-power value calculation unit 122 calculates the eye-refractive-power value as a prescription value based on the selected partial point image group.

12 and 13 show flow charts of an operation example of the ophthalmologic apparatus according to this embodiment.

(S1)
After the face of the subject is fixed by the face receiving portion, the head portion is moved to the inspection position of the eye E by the XY alignment by the XY alignment system 2 and the Z alignment by the Z alignment system 1. The inspection position is a position where the inspection of the eye E can be performed within a predetermined accuracy. For example, the processing unit 9 (main control unit 111) acquires an image pickup signal of the anterior segment image formed on the light receiving surface of the area sensor 56, and displays it on the display unit 170 (display screen 10a of the display unit 10). The eye image E'is displayed. After that, the head portion is moved to the inspection position of the eye E to be inspected by the above-mentioned XY alignment and Z alignment. The movement of the head unit is executed by the main control unit 111 according to an instruction from the main control unit 111, but may be executed by the main control unit 111 according to an operation or an instruction by the user.

(S2)
Next, the main control unit 111 executes temporary measurement (preliminary measurement). For example, the main control unit 111 causes the optotype chart 42 to display a fixation target such as a landscape chart. The main controller 111 causes the area sensor 76 to detect a point image group based on the return light from the eye E to be inspected obtained by turning on the light source 61. The main control unit 111 causes the eye-refractive-power value calculation unit 122 to calculate the eye-refractive-power value based on the point image group detected by the area sensor 76, and specifies the movement amount from the calculated eye-refractive-power value.

(S3)
The main control unit 111 moves the moving unit 46 along the optical axis to the position corresponding to the far point based on the moving amount calculated in S2.

(S4)
Next, the main control unit 111 executes the main measurement. First, the main controller 111 causes the area sensor 76 to newly detect a point image group based on the return light from the eye E to be inspected obtained by turning on the light source 61.

(S5)
The main control unit 111 numbers the point image group obtained in S4 and associates each point image with the lens array.

(S6)
Next, the main control unit 111 determines whether or not to obtain an eye refractive power value for each partial point image group based on the point image group acquired in S4.

In this embodiment, when a point image based on partial refractive error (refractive power change) exists in the point image group, the eye refractive power value is obtained for each partial point image group. The presence of a point image based on partial refractive error in the point image group means that a refractive error portion exists in the eye E (for example, the pupil). For example, if there is a partial refractive error, the distribution density of the point image formed on the light receiving surface of the area sensor 76 changes. The main control unit 111 identifies whether or not there is a point image based on the refractive error in the acquired point image group by identifying a region where the distribution density of the partial point image changes in the point image group acquired in S4. It is possible to determine whether or not. Specifically, the main control unit 111 determines whether or not the point image group acquired based on the density of point images per unit area has a point image based on partial refractive error. When it is determined that there is a point image based on the partial refractive error (S6:Y), the operation of the ophthalmologic apparatus proceeds to S11. When it is determined that there is no point image based on the refractive error (S6:N), the operation of the ophthalmologic apparatus proceeds to S7.

(S7)
When it is determined in S6 that the eye refractive power value is not obtained for each partial point image group (S6:N), the main control unit 111 further moves, for example, 1.5D from the position corresponding to the far point moved in S3. Only the moving unit 46 is moved to the far vision side in the optical axis direction, and the eye to be inspected is made to look at the visual target such as a landscape chart in a cloudy manner.

(S8)
Next, the main control unit 111 executes the measurement. First, the main controller 111 causes the area sensor 76 to newly detect a point image group based on the return light from the eye E to be inspected obtained by turning on the light source 61.

(S9)
The main control unit 111 causes the eye refractive power value calculation unit 122 to calculate a single eye refractive power value as a representative value based on the point images of the entire range of the measurement target acquired in S8. For example, the eye refractive power value calculation unit 122 obtains the eye refractive power value from the Zernike coefficient and the Zernike polynomial, as described above. Alternatively, the eye-refractive-power value calculation unit 122 calculates the eye-refractive-power value as described above for each of the two or more partial point image groups set from the point-image group, and based on the calculated two or more eye-refractive-power values. A single eye power value may be determined.

(S10)
The main control unit 111 causes the display unit 170 to display the single eye refractive power value as the representative value obtained in S9 or the representative value obtained in S24 described below. This is the end of the operation of the ophthalmologic apparatus (end).

(S11)
When it is determined in S6 that the eye refractive power value is to be calculated for each partial point image group (S6:Y), the main control unit 111 causes the eye refractive power value calculation unit 122 to calculate the eye refractive power value for each partial point image group. (Spherical power S, astigmatic power C, and astigmatic axis angle A) are calculated. That is, the main control unit 111 causes the setting unit 121 to set one or more partial point image groups from the point image group acquired in S4. After that, the main control unit 111 causes the eye refractive power value calculation unit 122 to calculate the eye refractive power value for each of the one or more partial point image groups set by the setting unit 121.

(S12)
The main control unit 111 determines whether or not the difference between the eye refractive power values obtained for each partial point image group is equal to or larger than a predetermined threshold value. When it is determined that the difference is equal to or greater than the predetermined threshold value (S12:Y), the operation of the ophthalmologic apparatus proceeds to S15. When it is determined that the difference is not greater than or equal to the predetermined threshold value (S12:N), the operation of the ophthalmologic apparatus shifts to 13.

(S13)
When it is determined that the difference is not greater than or equal to the predetermined threshold value in S12 (S12:N), the main control unit 111 further moves the moving unit 46 by, for example, 1.5D from the position corresponding to the far point moved in S3. The target chart 42 is moved to the far vision side in the optical axis direction to move to the cloud position.

(S14)
Next, the main control unit 111 executes the measurement. The main controller 111 causes the area sensor 76 to newly detect a point image group based on the return light from the eye E to be inspected obtained by turning on the light source 61.

(S15)
When it is determined in S12 that the difference is equal to or greater than the predetermined threshold value (S12:Y), the main control unit 111 moves the moving unit 46 to the myopia side by, for example, 2D, and searches for the adjustable range of the eye E to be inspected. To start.

(S16)
The main control unit 111 executes measurement. The main controller 111 causes the area sensor 76 to newly detect a point image group based on the return light from the eye E to be inspected obtained by turning on the light source 61.

(S17)
The main controller 111 causes the eye refractive power value calculator 122 to calculate the eye refractive power value for each of the partial point image groups. The main control unit 111 determines whether there is a partial point image group (corresponding part of the eye to be inspected) that matches the eye refraction value corresponding to the optotype presenting position. When it is determined that there is a partial point image group that matches the eye refraction value corresponding to the optotype presenting position (S17:Y), the operation of the ophthalmologic apparatus proceeds to S19. When it is determined that there is no partial point image group that matches the eye refraction value corresponding to the optotype presenting position (S17:N), the operation of the ophthalmologic apparatus proceeds to S18.

(S18)
When it is determined that there is no partial point image group that matches the eye refraction value corresponding to the optotype presenting position (S17:N), the main control unit 111 further moves the moving unit 46 to the myopia side by, for example, 1D. .. That is, the main control unit 111 determines that the position after the movement in S15 (or S18) is not within the adjustable range of the eye E, and continues the search for the range. The operation of the ophthalmologic apparatus shifts to S16.

(S19)
When it is determined in S17 that there is a partial point image group that matches the eye refraction value corresponding to the optotype presenting position (S17:Y), the main control unit 111 sets the moving unit 46 to the farsighted side by, for example, 0.25D. Just move. That is, the main control unit 111 determines that the position after movement in S15 (or S18) is within the adjustable range of the eye E, and starts searching for a position corresponding to the far point of the eye E. ..

(S20)
The main control unit 111 executes measurement. The main controller 111 causes the area sensor 76 to newly detect a point image group based on the return light from the eye E to be inspected obtained by turning on the light source 61.

(S21)
The main controller 111 causes the eye refractive power value calculator 122 to calculate the eye refractive power value for each of the partial point image groups. The main control unit 111 is a portion in which the change in the eye refractive power value in the partial point image group is equal to or less than a predetermined threshold with respect to the change in the eye refractive power value (hereinafter, reference change characteristic) corresponding to the change in the optotype presenting position. It is determined whether there is a point image. Here, the change in the eye refractive power value in the partial point image group corresponds to the change characteristics T1 and T2 in FIG. 11, and the reference change characteristic corresponds to the change characteristic T0. When it is determined that there is a partial point image group in which the error in the change of the eye refractive power value in the partial point image group with respect to the reference change characteristic is equal to or less than the predetermined threshold, the main control unit 111 determines that the error with respect to the reference change characteristic is the minimum. The selection unit 123 is caused to select the partial point image group.

When it is determined that the error in the change of the eye refractive power value in the partial point image group with respect to the reference change characteristic is not greater than or equal to the predetermined threshold value (S21:N), the operation of the ophthalmologic apparatus proceeds to S22. When it is determined that the error in the change in the eye refractive power value in the partial point image group with respect to the reference change characteristic is equal to or greater than the predetermined threshold value (S21:Y), the operation of the ophthalmologic apparatus proceeds to S19.

(S22)
When it is determined in S21 that the error in the change of the eye refractive power value in the partial point image group with respect to the reference change characteristic is not greater than or equal to the predetermined threshold value (S21:N), the main control unit 111 further performs, for example, 1.5D. Only the moving unit 46 is moved in the optical axis direction. That is, the main control unit 111 determines that the optotype presenting position corresponds to the far point, and moves the optotype chart 42 to the cloud position.

(S23)
The main control unit 111 executes measurement. The main controller 111 causes the area sensor 76 to newly detect a point image group based on the return light from the eye E to be inspected obtained by turning on the light source 61.

(S24)
The main control unit 111 causes the eye-refractive-power value calculation unit 122 to calculate eye-refractive-power values (spherical power S, astigmatic power C, and astigmatic axis angle A) for each of the partial point image groups acquired in S14. Alternatively, the main control unit 111 causes the eye refractive power value calculation unit 122 to calculate the eye refractive power values (spherical power S, astigmatic power C, and astigmatic axis angle A) for the partial point image group selected by the selection unit 123 in S21. Let it be calculated.

The eye-refractive-power value calculation unit 122 obtains a representative value (optimum correction value of the eye E) from the calculated one or more eye-refractive-power values. For example, the eye refractive power value calculation unit 122 calculates a representative value from two or more eye refractive power values calculated for one partial point image group. The eye-refractive-power value calculation unit 122 may also calculate the representative value from the two or more eye-refractive-power values calculated for the two or more partial point image groups. The operation of the ophthalmologic apparatus shifts to S10.

As described above, the ophthalmologic apparatus according to the embodiment irradiates the eye E with light from the light source 61 that is a point light source, acquires the point image group using the Hartmann plate 75, and extracts the point image group from the acquired point image group. One or more partial point image groups are set, and the eye refractive power value is obtained for each of the set one or more partial point image groups. As a result, the eye refractive power value of the part that actually contributes to the perception of the subject can be calculated as compared with the case where the entire measurement region is approximated to one curved surface and the eye refractive power value is calculated. It is possible to obtain a high eye refractive power value.

Further, the ophthalmologic apparatus according to the embodiment, with respect to the change in the eye refractive power value corresponding to the change in the optotype presenting position, the partial point image group in which the error in the change in the eye refractive power value in the partial point image group is the minimum. The eye refractive power value is calculated based on. This makes it possible to obtain a highly reliable prescription value even when there is a refractive error area in the pupil.

The ophthalmologic apparatus according to the embodiment can calculate the eye refractive power value for each zone for the zone-type multifocal intraocular lens inserted eye. This makes it possible to easily determine whether or not an appropriate intraocular lens has been inserted into the eye into which the intraocular lens has been inserted.

(Action/effect)
The operation and effect of the ophthalmologic apparatus according to the embodiment will be described.

The ophthalmologic apparatus according to the embodiment includes a measurement optical system (aberration measurement projection system 6 and aberration measurement light reception system 7), a fixation optical system (target projection system 4), a moving mechanism (moving mechanism 46A), and a controller. The control unit 110 and the main control unit 111 include a setting unit (setting unit 121), a calculation unit (eye refractive power value calculation unit 122), and a selection unit (selection unit 123). The measurement optical system projects the measurement light onto the fundus (fundus Ef) of the eye to be examined (eye E), generates a plurality of focused lights from the return light of the measurement light from the fundus, and generates the plurality of focused lights. It receives light and detects a point image group. The fixation optical system presents a fixation target to the eye to be examined. The moving mechanism moves the fixation target in the perspective direction. The control unit causes the measurement optical system to detect the point image group at each of the plurality of positions in the perspective direction by cooperatively controlling the moving mechanism and the measurement optical system. The setting unit sets two or more partial point image groups from each of the plurality of point image groups acquired by the coordinated control. The calculation unit obtains an eye refractive power value based on each partial point image group set by the setting unit. The selection unit selects one of the two or more partial point image groups based on the change of the eye refractive power value for each partial point image group in the perspective direction. The calculation unit obtains an eye refractive power value based on the partial point image group selected by the selection unit.

According to such a configuration, two or more partial point image groups of the point image group acquired by projecting the measurement light on the fundus of the eye are used to change the eye refractive power values of the two or more partial point image groups in the perspective direction. Since one of the partial point image groups is selected and the eye refractive power value of the selected partial point image group is obtained, even if there is a refractive error part in the eye to be examined, it is possible to perceive the subject's perception. It is possible to obtain the eye refractive power value in the contributing region as a prescription value.

Further, in the ophthalmologic apparatus according to the embodiment, the selection unit may select the partial point image group having the smallest error with respect to the eye refractive power values corresponding to the plurality of positions.

With such a configuration, it is possible to obtain a highly reliable prescription value even when a refractive error portion exists in the eye to be inspected.

Further, in the ophthalmologic apparatus according to the embodiment, before the coordinated control, the control unit causes the measurement optical system to perform preliminary measurement for detecting the point image group, and the calculation unit causes the point image acquired by the preliminary measurement. Obtaining a plurality of eye refractive power values based on a plurality of partial point image group of the group, the control unit obtains a value representing the variation of the plurality of eye refractive power value, when the value is equal to or more than a threshold value, a coordinated The control may be performed, and when the value is less than the threshold value, the default control of the measurement optical system may be performed.

With such a configuration, it is possible to obtain a highly reliable prescription value corresponding to the variation (difference, etc.) in the eye refractive power value between the partial point image groups.

Further, in the ophthalmologic apparatus according to the embodiment, as the default control, the control unit causes the measurement optical system to detect the point image group, and the calculation unit sets 1 based on one or more partial point image groups of the point image group. The above eye refractive power values may be obtained.

According to such a configuration, for example, when the value representing the variation in the eye refractive power value between the partial point image groups is less than the threshold value, for example, it is determined that the eye to be inspected does not have a refractive error site, and each partial point image group is determined. The eye refractive power value can be obtained. As a result, the eye refractive power value of the part that actually contributes to the perception of the subject can be calculated, as compared to the case where the entire measurement target area is approximated to one curved surface and the eye refractive power value is calculated. It is possible to obtain a highly reliable eye refractive power value.

In the ophthalmologic apparatus according to the embodiment, when the point image group has a point image based on partial refractive error, the calculation unit calculates one or more eye refractive power values based on the one or more partial point image groups. If there is no point image based on the partial refractive error in the point image group, a single eye refractive power value may be obtained based on the point image group.

According to such a configuration, the eye refractive power value is obtained for each of the one or more partial point image groups or the single point image group is calculated for each of the point image groups according to the presence or absence of the point image based on the partial refractive error in the point image group. Since one eye refractive power value is obtained, it is possible to calculate the eye refractive power value with high reliability.

Further, in the ophthalmologic apparatus according to the embodiment, the measurement optical system may include a lens array that generates a plurality of focused lights from the return light, and an area sensor that receives the plurality of focused lights generated by the lens array. ..

With such a configuration, the optical system of the ophthalmologic apparatus capable of measuring the wavefront aberration can be diverted, so that it is possible to obtain a highly reliable prescription value at low cost.

Further, in the ophthalmologic apparatus according to the embodiment, the eye refractive power value may include a spherical power, an astigmatic power, and an astigmatic axis angle.

With such a configuration, it is possible to obtain the spherical power, the astigmatic power, and the astigmatic axis angle of the part that actually contributes to the subject's perception even when there is a refractive error part in the subject's eye.

(Other modifications)
The embodiments described above are merely examples for implementing the present invention. A person who intends to carry out the present invention can make arbitrary modifications, omissions, additions, etc. within the scope of the present invention.

The above embodiment is applied to a device having any function that can be used in the field of ophthalmology, such as an intraocular pressure measurement function, a fundus imaging function, an anterior segment imaging function, an optical coherence tomography (OCT) function, and an ultrasonic examination function. The invention according to can be applied. The tonometry function is realized by a tonometer or the like. The fundus photographing function is realized by a fundus camera, a scanning ophthalmoscope (SLO), or the like. The anterior segment imaging function is realized by a slit lamp or the like. The OCT function is realized by an optical coherence tomography device or the like. The ultrasonic inspection function is realized by an ultrasonic diagnostic device or the like. Further, the present invention can be applied to an apparatus (multifunction machine) having two or more of such functions.

4 Target projection system 5 Observation system 6 Aberration measurement projection system 7 Aberration measurement light receiving system 46A Moving mechanism 75 Hartmann plate 76 Area sensor 110 Control unit 111 Main control unit 120 Calculation processing unit 121 Setting unit 122 Eye refractive power value calculating unit 123 Selection Department

Claims (7)

Measuring optics for projecting measurement light onto the fundus of the eye to be examined, generating a plurality of focused lights from return light of the measurement light from the fundus, and receiving the plurality of generated focused lights to detect a point image group. System,
A fixation optical system that presents a fixation target to the eye to be examined,
A moving mechanism for moving the fixation target in the perspective direction,
A control unit that causes the measurement optical system to detect the point image group at each of the plurality of positions in the perspective direction by cooperatively controlling the moving mechanism and the measurement optical system,
A setting unit that sets two or more partial point image groups from each of the plurality of point image groups acquired by the coordinated control;
A calculating unit for obtaining an eye refractive power value based on each of the partial point image groups set by the setting unit,
A selection unit that selects one of the two or more partial point image groups based on a change in the eye refractive power value for each partial point image group in the perspective direction;
Including
The ophthalmologic apparatus, wherein the calculation unit obtains an eye refractive power value based on the partial point image group selected by the selection unit. The ophthalmologic apparatus according to claim 1, wherein the selection unit selects a partial point image group having a minimum error with respect to eye refractive power values corresponding to the plurality of positions. Before the coordinated control, the control unit causes the measurement optical system to perform preliminary measurement for detecting a point image group,
The calculation unit obtains a plurality of eye refractive power values based on a plurality of partial point image groups of the point image group acquired by the preliminary measurement,
The control unit obtains a value representing the variation of the plurality of eye refractive power values, when the value is equal to or more than a threshold value, executes the coordinated control, and when the value is less than the threshold value, the measurement optical The ophthalmologic apparatus according to claim 1 or 2, which executes predetermined control of the system. As the predetermined control, the control unit causes the measurement optical system to detect a point image group,
The ophthalmologic apparatus according to claim 3, wherein the calculation unit obtains one or more eye refractive power values based on one or more partial point image groups of the point image group. The calculation unit,
When the point image group has a point image based on partial refractive error, the one or more eye refractive power values are obtained based on the one or more partial point image groups,
The ophthalmologic apparatus according to claim 4, wherein when the point image group has no point image based on partial refractive error, a single eye refractive power value is obtained based on the point image group. The measurement optical system,
A lens array that generates the plurality of focused lights from the return light,
An area sensor for receiving the plurality of focused lights generated by the lens array,
The ophthalmologic apparatus according to any one of claims 1 to 5, further comprising: The ophthalmic apparatus according to any one of claims 1 to 6, wherein the eye refractive power value includes a spherical power, an astigmatic power, and an astigmatic axis angle.

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