JP2019055122A - Ophthalmologic apparatus - Google Patents

Abstract

To provide an ophthalmologic apparatus having a wider alignable range to allow the measurement of cornea geometries with high precision.SOLUTION: The ophthalmologic apparatus includes: two or more imaging units for imaging the anterior eye part of a subject eye substantially at the same time from different directions; and an optical member in which are formed a diffuse-transmission part for a predetermined pattern and two or more transparent parts through which the optical path of the two or more imaging units passes. The ophthalmologic apparatus further includes: a projection unit for projecting, onto the anterior eye part, measurement pattern light obtained by light from a light source disposed to the rear side of the optical member diffuse-transmitting through the diffuse-transmission part; a cornea geometry information acquisition unit for acquiring cornea geometry information of the subject eye based on an image of the anterior eye part onto which the measurement pattern light is projected by the projection unit; and a movement amount determination unit for determining the amount of movement of the projection unit based on two or more projection images captured by the two or more imaging units. An entrance pupil for each of the two or more imaging units is arranged in or near the corresponding transparent unit.SELECTED DRAWING: Figure 1

Description

  The present invention relates to an ophthalmologic apparatus that obtains information about an eye to be examined by projecting a measurement pattern onto the eye to be examined.

  The measurement result of the corneal surface shape by an ophthalmologic apparatus having a corneal shape measurement function is used for diagnosis of corneal diseases such as keratoconus, surgery for eye diseases such as cataract, and prescription of contact lenses. Such an ophthalmologic apparatus projects a ring-shaped measurement pattern on the cornea of the eye to be examined, receives reflected light from the cornea of the measurement pattern, and information on the shape of the cornea from changes in the shape of the reflected light with respect to the projected measurement pattern (See, for example, Patent Document 1 and Patent Document 2).

  Similar to the measurement using the imaging of the eye and optical coherence tomography (OCT), the corneal shape is measured between the apparatus optical system and the eye to be measured from the viewpoint of measurement accuracy and accuracy. Alignment is extremely important. This alignment is called alignment. The alignment includes an operation for aligning the optical axis of the apparatus optical system with the axis of the eye to be examined (XY alignment) and an operation for adjusting the distance between the eye to be examined and the apparatus optical system (Z alignment).

  There are various methods for alignment. As a technique realized in recent years, two or more captured images obtained by photographing the anterior segment of the eye to be examined from different directions are analyzed to identify the three-dimensional position of the eye to be examined, and XY based on this three-dimensional position There is a technique for performing both alignment and Z alignment (see, for example, Patent Document 3). According to this method, an alignment with a wide alignment range (dynamic range) can be performed by acquiring an image with a wide viewing angle. Therefore, by using this method, alignment can be performed using an image photographed at a certain distance from the eye to be examined.

JP 62-034526 A JP 2011-167359 A JP 2013-248376 A

  In an ophthalmologic apparatus having a corneal shape measurement function, a plate (kerato plate, platide plate) on which a diffuse transmission part having a predetermined measurement pattern is formed is placed in front of the eye. The light from the light source arranged on the back side of the plate (opposite to the eye to be inspected) diffuses and transmits through the diffusing and transmitting part, so that, for example, ring-shaped measurement pattern light is projected onto the cornea of the eye to be inspected.

  When such an ophthalmologic apparatus performs alignment using the two or more captured images, there are the following problems.

  Since the ring diameter of the measurement pattern light projected on the cornea is determined by the incident angle of the measurement pattern light on the cornea, the ring diameter of the measurement pattern light is determined by the position of the plate with respect to the eye to be examined. On the other hand, with respect to the positions of two or more photographing units, the alignment sensitivity and the alignment possible range are determined depending on the angle at which the anterior segment is viewed. Therefore, it is difficult to arrange two or more imaging units at arbitrary positions with a ring diameter of a desired measurement pattern light, and it is difficult to arrange a plate at a position outside the imaging optical path of the imaging unit. As a result, it is necessary to arrange a plate in which a light transmitting portion (opening) is formed in the photographing optical path so that the photographing optical path of the photographing unit passes.

  When the size of the translucent part formed on the plate is increased, a captured image with a sufficiently wide field of view can be acquired. However, since the translucent part is formed in the region of the diffuse transmissive part, the measurement pattern is lost, and it becomes impossible to project the measurement pattern light onto the cornea in a specific meridian range. In this case, the measurement result of the corneal shape in the meridian range cannot be obtained. For example, by approximating the pattern image based on the reflected light of the measurement pattern light to a circle or ellipse, the information on the meridian range can be supplemented, or the information on the pattern image inside or outside the opening can be supplemented. However, the error becomes large especially in corneal irregular astigmatism and keratoconus.

  On the other hand, if the size of the translucent part formed on the plate is reduced, the translucent part can be easily formed in a region other than the region of the diffuse transmissive part. However, light with an angle of view is easily vignetted, resulting in a narrow alignment range.

  The present invention has been made in view of such circumstances, and an object thereof is to provide an ophthalmologic apparatus capable of measuring a corneal shape with a wide alignment range and high accuracy.

  In the first aspect of the embodiment, two or more imaging units that image the anterior segment of the eye to be examined substantially simultaneously from different directions, a diffuse transmission unit having a predetermined pattern, and an optical path of the two or more imaging units pass. An optical member formed with two or more light-transmitting portions, and the measurement pattern light obtained by diffusing and transmitting light from a light source disposed on the back side of the optical member through the diffusion-transmitting portion A projection unit that projects onto an eye unit, a corneal shape information acquisition unit that obtains corneal shape information of the eye to be inspected based on an image of the anterior segment on which the measurement pattern light is projected by the projection unit, and the two or more A movement amount determination unit that determines a movement amount of the projection unit based on two or more captured images acquired by the imaging unit, and each entrance pupil of the two or more imaging units has a corresponding light transmission Ophthalmic equipment placed at or near the head It is.

  Further, in the second aspect of the embodiment, in the first aspect, at least one of the two or more photographing units has a front main plane arranged at or near the corresponding light transmitting part among the two or more light transmitting parts. And an imaging device disposed on the rear side of the lens.

  In the third aspect of the embodiment, in the first aspect, at least one of the two or more photographing units is a microlens disposed in a corresponding light transmitting part or the vicinity thereof among the two or more light transmitting parts. And an image sensor disposed on the rear side of the microlens.

  In the fourth aspect of the embodiment, the two or more light transmitting parts may include an optical system that includes an opening, an optical axis passes through the opening, and acquires data of the anterior eye part.

  Further, in a fifth aspect of the embodiment, in any one of the first aspect to the third aspect, an opening is formed in the optical member, and an anterior axis is disposed so that an optical axis passes through the opening. The two or more translucent portions may be formed at a position that is asymmetric with respect to a position corresponding to the optical axis in the opening.

  In the sixth aspect of the embodiment, in the fifth aspect, the two or more light-transmitting portions may be formed below the optical axis.

  Moreover, the 7th aspect of embodiment is the drive part which relatively moves the support part which supports a subject's face in any one of the 4th aspect-the 6th aspect, and the said optical system and the said support part. And a control unit that moves the optical system and the support unit relative to each other by controlling the drive unit based on the movement amount.

  In the eighth aspect of the embodiment, in any one of the first to seventh aspects, the two or more light-transmitting portions may be formed at positions that do not overlap with the diffuse transmission portion.

  In the ninth aspect of the embodiment, in any one of the first to eighth aspects, the predetermined pattern may be a ring pattern or a concentric pattern.

  In addition, it is possible to combine arbitrarily the structure which concerns on the above-mentioned several aspect.

  According to the present invention, it is possible to provide an ophthalmologic apparatus capable of measuring a corneal shape with a wide alignment range and high accuracy.

It is a schematic diagram showing an example of composition of an ophthalmology device concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmology device concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmology device concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmology device concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmology device concerning an embodiment. It is the schematic showing an example of the structure of the ophthalmologic apparatus which concerns on the comparative example of embodiment. It is the schematic showing an example of the structure of the ophthalmologic apparatus which concerns on the comparative example of embodiment. It is the schematic showing an example of operation | movement of the ophthalmologic apparatus which concerns on the comparative example of embodiment. It is a schematic diagram showing an example of composition of an ophthalmology device concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmology device concerning an embodiment. It is the schematic showing an example of operation | movement of the ophthalmologic apparatus which concerns on embodiment. It is the schematic of the flow showing an example of operation | movement of the ophthalmologic apparatus which concerns on embodiment. It is the schematic showing an example of the structure of the ophthalmologic apparatus which concerns on the modification of 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. The ophthalmologic apparatus according to the embodiment has a corneal shape measuring function for optically measuring the corneal shape of the eye to be examined. Such ophthalmic devices include corneal shape measurement functions, ophthalmic imaging functions such as optical coherence tomometers, fundus cameras, and scanning laser ophthalmoscopes, eye refraction inspection devices, tonometers, specular microscopes, wave front analyzers. It may have an ophthalmic measurement function.

  In the following embodiment, a case will be described in which information representing the corneal shape of the eye E is acquired using a kerato ring image obtained by projecting kerato ring on the cornea. However, the ophthalmologic apparatus according to the embodiment may acquire information representing the cornea shape of the eye E using a placido ring image obtained by projecting a pracido ring on the cornea.

  Any known technique, including techniques disclosed in the documents cited in this specification, can be combined with the embodiments.

<Configuration>
1 to 5 show a configuration example of an ophthalmologic apparatus according to the embodiment. The ophthalmologic apparatus 1 has a function of acquiring information related to the corneal shape of the eye E to be examined. The ophthalmic apparatus 1 can acquire information on the corneal shape after aligning the apparatus optical system with respect to the eye E.

  The ophthalmologic apparatus 1 includes a control unit 11, a data processing unit 12, an optical unit 20, a face support unit 70, a first drive unit 80A, a second drive unit 80B, and a user interface (UI) unit 90. Including. Note that the configuration may be such that only one of the first drive unit 80A and the second drive unit 80B is provided. Typically, the ophthalmologic apparatus 1 may include only the first drive unit 80A.

  Each of the control unit 11 and the data processing unit 12 includes a processor. 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 LD). (Field Programmable Gate Array)). The functions of both the control unit 11 and the data processing unit 12 may be realized by a single processor.

  For example, the processor implements the functions according to the embodiment by reading and executing a program stored in a storage circuit or a storage device. At least a part of the memory circuit or the memory device may be included in the processor. Further, at least a part of the memory circuit or the memory device may be provided outside the processor.

  The storage device or the like stores various data. Examples of data stored in the storage device include data acquired by the measurement optical system 30 and the anterior segment camera 60 (measurement data, imaging data, etc.), information on the subject and the subject's eye, and the like. The storage device or the like may store various computer programs and data for operating the ophthalmologic apparatus 1.

(Control unit 11)
The control unit 11 executes control of each unit of the ophthalmologic apparatus 1. In particular, the control unit 11 controls the data processing unit 12, the optical unit 20, the first driving unit 80A, the second driving unit 80B, and a user interface (UI) unit 90. The control unit 11 includes an alignment control unit 111 and a UI control unit 112.

(Alignment control unit 111)
The alignment control unit 111 executes control related to alignment. The ophthalmologic apparatus 1 identifies the three-dimensional position of the eye E by analyzing two or more captured images obtained by photographing the anterior eye portion Ea of the eye E from different directions, and uses the identified three-dimensional position. It is possible to perform the alignment used. Two or more captured images used for alignment are acquired by an anterior eye camera 60 described later. When the measurement optical system 30 includes an anterior ocular segment imaging system, two or more captured images used for alignment may be acquired by the anterior segment camera 60 and the measurement optical system 30.

  Further, the alignment control unit 111 may be capable of executing the above-described alignment and alignment (manual alignment) manually performed by the examiner. The alignment control unit 111 can perform processing for selecting an alignment mode corresponding to the alignment operation and control of each unit in the selected alignment mode.

(UI control unit 112)
The UI control unit 112 performs control related to the user interface unit 90. In other words, the UI control unit 112 performs control related to the exchange of information between the ophthalmologic apparatus 1 and the user. Typically, the UI control unit 112 executes control for displaying information on the display unit 91 and control according to an operation performed using the operation unit 92. The information output mode by the ophthalmologic apparatus 1 is not limited to display output, and may include sound output, print output, lighting of a light emitting diode, and the like.

(Data processing unit 12)
The data processing unit 12 executes various data processing. For example, the data processing unit 12 analyzes an image of the anterior segment of the eye E acquired by the measurement optical system 30. The analysis result of the anterior eye image is used to acquire corneal shape information. For example, the data processing unit 12 analyzes an image acquired by the anterior eye camera 60. The analysis result of the image is used for alignment or the like.

(Optical unit 20)
The optical unit 20 stores a configuration for measuring and / or photographing the eye E and a configuration for preparing the same. The former includes the measurement optical system 30 and the latter includes the anterior eye camera 60. The anterior eye camera 60 is used in alignment.

  The optical unit 20 is provided with a measurement optical system 30, a kerato plate 40, and an anterior eye camera 60. The anterior eye camera 60 is installed on the surface of the housing of the optical unit 20 or a part of the anterior eye camera 60 is exposed on the surface of the housing.

  In addition to the configuration shown in FIG. 1, the optical unit 20 may be provided with an optical system (illumination optical system, observation optical system, photographing optical system, etc.) for photographing the eye E from the front. Further, a configuration for performing focusing of the measurement optical system 30 may be provided.

(Measurement optical system 30)
The measurement optical system 30 includes a configuration for acquiring data of the eye E and / or a configuration for imaging the eye E. The measurement optical system 30 is configured according to the functions (measurement function, imaging function, etc.) provided by the ophthalmologic apparatus 1. In this embodiment, the measurement optical system 30 includes an objective lens and an anterior segment imaging system (imaging lens, image sensor) that captures the anterior segment Ea of the eye E to be examined. The anterior segment imaging system acquires an image in which an image (pattern image) based on the reflected light of the measurement pattern light is drawn by photographing the cornea of the eye E to which the measurement pattern light is projected as described later. To do. For example, the measurement optical system 30 includes a light source, an optical element (an optical member, an optical device), an actuator, a mechanism, a circuit, a display device, a light receiving element, an image sensor, and the like.

  The measurement optical system 30 may include a configuration for providing a function associated with the inspection. For example, a fixation optical system for projecting a target (fixation target) for fixing the eye E on the fundus of the eye E may be provided.

(Detection of the position of the optical unit 20)
The ophthalmologic apparatus 1 has a function of detecting the position of the optical unit 20. For example, the control unit 11 can record the content of control for the first drive unit 80A and / or the second drive unit 80B, and can determine the position of the measurement optical system 30 from this record (control history). In another example, the ophthalmologic apparatus 1 includes a position sensor that detects the position of the optical unit 20.

  Based on the relative position between the optical unit 20 and the reference position in the eye E determined by the data processing unit 12, the control unit 11 (alignment control unit 111 or the like) performs the first drive unit 80A and / or the second drive. The unit 80B can be controlled. Thereby, the optical unit 20 can be moved to a predetermined position with respect to the reference position in the eye E.

  In this embodiment, the alignment includes Z alignment and XY alignment. The Z alignment is an alignment in the optical axis direction (Z direction) of the measurement optical system 30. XY alignment is alignment in the X direction (horizontal direction) and Y direction (vertical direction) orthogonal to the Z direction.

  Each of the XY alignment and the Z alignment is executed by analyzing two or more captured images obtained substantially simultaneously by two or more anterior segment cameras 60.

  In addition, an image of the anterior segment Ea acquired by one of the two or more anterior segment cameras 60 (in other words, acquired by the anterior segment camera 60 arranged at a position off the optical path of the measurement optical system 30). Image processing for converting an image, that is, an image acquired by photographing the anterior segment Ea from an oblique direction into an image viewed from the front can be applied. This processing is, for example, viewpoint conversion based on the expected angle of the anterior eye camera 60 (the position of the anterior eye camera 60). XY alignment and Z alignment can be performed using a front image formed through such image processing.

  In the case of manual alignment, the UI control unit 112 displays the image of the anterior segment Ea and the alignment mark on the display unit 91, and the user operates the operation unit 92 so as to satisfy a predetermined alignment condition. In manual alignment, the UI control unit 112 can cause the display unit 91 to display information for assisting the user's operation. For example, information indicating the alignment shift direction and / or the shift amount can be displayed, and the direction and / or amount in which the optical unit 20 should be moved can be displayed.

  In the case of auto-alignment, the data processing unit 12 calculates the displacement of the characteristic position (for example, the corneal apex or the pupil region) in the anterior segment Ea with respect to the alignment mark, and the alignment control unit 111 cancels the displacement. Are moved in the XY and Z directions.

(Kerato board 40)
The kerato plate 40 is disposed on the front surface of the optical unit 20 (the surface facing the eye E). The kerato plate 40 is formed with a diffuse transmission part having a predetermined measurement pattern and two or more light transmission parts through which the photographing optical path of the anterior eye camera 60 passes. The translucent part may be an opened part. In addition, the light transmitting portion may be provided with an optical element that transmits light.

  When the anterior ocular segment imaging system provided in the measurement optical system 30 also serves as one of the anterior ocular segment cameras 60, the two or more translucent units may include an opening through which the optical axis of the measurement optical system 30 passes. Good. In this case, since only one opening and one light transmitting part need be formed in the kerato plate 40 in addition to the diffuse transmission part, the degree of freedom of arrangement of the light transmitting part through which the imaging optical path passes is improved. This makes it easier to avoid missing measurement patterns.

  Hereinafter, the case where one opening and two light transmitting parts are formed on the kerato plate 40 in addition to the diffuse transmitting part (that is, when two anterior eye cameras 60 are used) will be described.

  The measurement pattern is, for example, a ring pattern or a concentric circle pattern. Further, the measurement pattern may be, for example, an ellipse pattern, an arbitrary curve pattern, an arbitrary linear pattern, or the like. Furthermore, the measurement pattern may not be a closed curve. For example, the measurement pattern may be a part of a circle, a part of a concentric circle, a part of an ellipse, or the like. The measurement pattern may be a planar pattern having a two-dimensional extension.

  The measurement pattern may be a discrete pattern instead of a continuous pattern such as a ring pattern or a concentric circle pattern.

  The discrete pattern may include an arbitrary number of dot patterns, an arbitrary number of linear patterns, an arbitrary number of planar patterns, and the like.

  A light source (not shown) is disposed on the back side of the kerato plate 40 (the side opposite to the eye E). The light source may be a light emitting device or a combination of a light emitting device and an optical element. A typical example of a light-emitting device is a light-emitting diode (LED) that emits light in the near-infrared region (for example, the center wavelength is 950 nm), which is invisible light. The light emitting device may have a shape corresponding to the measurement pattern (diffuse transmission part). In addition, the kerato plate 40 may be provided with a plurality of light emitting devices arranged according to the measurement pattern.

  As described above, the light from the light source arranged on the back side of the kerato plate 40 diffuses and transmits through the diffusing and transmitting part, whereby a predetermined measurement pattern light is projected onto the anterior eye part Ea of the eye E to be examined. The projection image is used to acquire corneal shape information of the eye E.

  The corneal shape information includes, for example, an arbitrary parameter value representing the shape of the cornea that can be measured using a known ophthalmic apparatus. Typically, the corneal shape information includes the radius of curvature (curvature), the direction of the strong main meridian, the radius of curvature along the strong main meridian (frequency), the direction of the weak main meridian, the radius of curvature (frequency) along the weak main meridian, Any of ellipticity, eccentricity, flatness, topography including irregular astigmatism, aberration information using Zernike polynomials, and the like may be included.

(Anterior eye camera 60)
Two or more anterior eye cameras 60 are provided at different positions. Each anterior eye camera 60 is, for example, a video camera that performs moving image shooting at a predetermined frame rate. The two or more anterior segment cameras 60 photograph the anterior segment substantially simultaneously from different directions.

  In the example shown in FIG. 1, it is provided at a position off the optical path of the measurement optical system 30 or the like, but is not limited to this. For example, when the measurement optical system 30 is provided with an anterior segment imaging system (for example, an image sensor), one of the two or more anterior segment cameras may be the anterior segment imaging system.

  3 and 4 schematically show the anterior eye camera 60 in the ophthalmologic apparatus 1 according to the embodiment. FIG. 3 schematically shows a view of the optical system of the ophthalmologic apparatus 1 as viewed from above. FIG. 4 schematically shows a view of the optical system of the ophthalmologic apparatus 1 viewed from the side. 3 and 4, the same parts as those in FIG.

  In this embodiment, for example, as shown in FIG. 3, two anterior eye cameras 60A and 60B are provided. 3 is a top view, and the + Y direction indicates a vertically upward direction, and the + Z direction indicates the optical axis direction of the measurement optical system 30 and the direction from the measurement optical system 30 toward the eye E. FIG. Further, the anterior eye cameras 60 </ b> A and 60 </ b> B are provided at positions deviating from the optical path of the measurement optical system 30. Hereinafter, the two anterior eye cameras 60 </ b> A and 60 </ b> B may be collectively represented by the symbol “60”.

  The number of the anterior segment camera may be an arbitrary number of 2 or more as long as the anterior segment can be photographed substantially simultaneously from two different directions. One anterior eye camera may be arranged coaxially with the measurement optical system 30.

  “Substantially simultaneously” indicates that, for example, in photographing with two or more anterior segment cameras, a deviation in photographing timing that allows negligible eye movement is allowed. Thereby, an image when the eye E is substantially at the same position (orientation) can be acquired by two or more anterior segment cameras.

  In addition, although shooting with two or more anterior eye cameras may be moving image shooting or still image shooting, in this embodiment, a case where moving image shooting is performed will be described in detail. In the case of moving image shooting, the above-described substantially simultaneous anterior ocular shooting can be realized by controlling the shooting start timing to match or by controlling the frame rate and shooting timing of each frame. On the other hand, in the case of still image shooting, this can be realized by controlling to match the shooting timing.

  At least one of the two or more anterior eye cameras 60 includes an imaging lens 61 in which the front main plane is arranged in the corresponding translucent part or in the vicinity thereof, and imaging arranged on the rear side (emission side) from the imaging lens 61. Element 62. The entrance pupil of each anterior segment camera 60 is disposed at or near the corresponding translucent portion. Thereby, the size of the translucent part can be reduced as much as possible to almost the same size as the entrance pupil. Therefore, it becomes easy to form the light transmitting portion by avoiding the diffuse transmitting portion in the kerato plate 40, and projecting the measurement pattern light having no defective portion or a small defective region onto the cornea of the eye E to be examined even when there is a defective portion. Will be able to. Furthermore, since the anterior eye camera 60 has a small vignetting and can capture a captured image with a sufficiently wide field of view, it is possible to achieve alignment with a wide dynamic range by using two or more captured images. become.

  For example, an anterior eye camera 60A is disposed on the left side of an objective lens (not shown) provided in the measurement optical system 30, and an anterior eye camera 60B is disposed on the right side. In this embodiment, as shown in FIG. 4, anterior eye cameras 60A and 60B are disposed below (−Y direction) the lens center of the objective lens (the optical axis O of the measurement optical system 30). Therefore, in the kerato plate 40, the two or more light transmitting portions are formed below the optical axis of the measurement optical system 30 in the opening. Thereby, it is possible to reduce the possibility that the subject's eyelashes or eyelashes appear in the captured images acquired by the anterior eye cameras 60A and 60B. Moreover, even if the subject has a deep eye depression (orbit), anterior segment imaging can be suitably performed.

(Face support part 70)
The face support unit 70 includes a member for supporting the subject's face. For example, the face support unit 70 includes a forehead pad on which the subject's forehead abuts and a chin rest on which the subject's chin is placed. The face support unit 70 may include only one of the forehead support and the chin rest, or may include other members.

(First driving unit 80A and second driving unit 80B)
The first drive unit 80A moves the optical unit 20 under the control of the control unit 11 (alignment control unit 111 or the like). The first drive unit 80A can move the optical unit 20 three-dimensionally. The first drive unit 80A includes, for example, a mechanism for moving the optical unit 20 in the X direction, a mechanism for moving in the Y direction, and a mechanism for moving in the Z direction, as in the conventional case. The first drive unit 80A may include a rotation mechanism that rotates the optical unit 20 within a plane (horizontal plane, vertical plane, etc.) including the optical axis of the optical unit 20.

  The second drive unit 80B moves the face support unit 70 under the control of the control unit 11 (alignment control unit 111 or the like). The second drive unit 80B can move the face support unit 70 three-dimensionally. The second drive unit 80B includes, for example, a mechanism for moving the face support unit 70 in the X direction, a mechanism for moving in the Y direction, and a mechanism for moving in the Z direction. The second drive unit 80B may include a rotation mechanism for changing the orientation of the face support unit 70 (or a member included therein). When a plurality of members are provided in the face support unit 70, the second drive unit 80B may be configured to move these members individually. For example, the second drive unit 80B may be configured to move the forehead rest and the chin rest individually or only one of them.

(User interface unit 90)
The user interface unit 90 provides functions for exchanging information between the ophthalmologic apparatus 1 and the user, such as information display, information input, and operation instruction input. The user interface unit 90 provides an output function and an input function. The user interface unit 90 is controlled by the UI control unit 112.

  A display unit 91 is a typical example of a configuration that provides an output function. The display unit 91 includes a display device such as a flat panel display. Other examples of the configuration related to the output function include an audio output device and a light emitting diode.

  A typical example of a configuration that provides an input function is an operation unit 92. The operation unit 92 includes operation devices such as a lever, a button, a key, and a pointing device. Other examples of the configuration related to the input function include a microphone and a data writer.

  The user interface unit 90 may include a device in which an output function and an input function such as a touch panel display are integrated. The user interface unit 90 may include a graphical user interface (GUI) for inputting and outputting information.

(Details of the data processing unit 12)
Details of the data processing unit 12 will be described. As shown in FIG. 2, the data processing unit 12 includes an image correction unit 121, a feature position specifying unit 122, a three-dimensional position calculation unit 123, a movement amount determination unit 124, and a corneal shape information acquisition unit 125. Is provided.

(Image correction unit 121)
The image correction unit 121 corrects the distortion of the captured image obtained by the anterior eye camera 60 based on predetermined aberration information. This process is executed by, for example, a known image processing technique based on a correction coefficient for correcting distortion. Note that it is not necessary to provide the image correction unit 121 when the distortion aberration given to the captured image by the optical system of the anterior eye camera 60 is sufficiently small.

  The aberration information is stored in advance in a storage device or the like provided in the ophthalmologic apparatus 1, for example. Alternatively, the ophthalmologic apparatus 1 can be configured to refer to aberration information stored in advance in an external device. In the aberration information, information on distortion aberration generated in the captured image due to the influence of the optical system mounted on each anterior eye camera 60 is recorded. Here, the optical system mounted on the anterior eye camera 60 includes an optical element that generates distortion, such as a lens. The aberration information can be said to be a parameter obtained by quantifying the distortion that these optical elements give to the photographed image.

  An example of a method for generating aberration information will be described. Taking the instrumental difference (difference in distortion) of the anterior segment camera 60 into consideration, the following measurement is performed for each anterior segment camera 60. The operator prepares a predetermined reference point. The reference point is an imaging target used for detecting distortion. The operator performs shooting a plurality of times while changing the relative position between the reference point and the anterior eye camera 60. Thereby, a plurality of captured images of the reference point captured from different directions are obtained. The operator generates aberration information for the anterior eye camera 60 by analyzing a plurality of acquired images with a computer.

The analysis process for generating aberration information includes, for example, the following steps.
An extraction process for extracting an image area corresponding to a reference point from each captured image. A distribution state calculation process for calculating a distribution state (coordinates) of an image area corresponding to the reference point in each captured image. Based on the obtained distribution state A distortion aberration calculating step for calculating a parameter representing distortion aberration and a correction coefficient calculating step for calculating a coefficient for correcting the distortion aberration based on the obtained parameter

  Parameters relating to distortion aberration given to an image by the optical system include principal point distance, principal point position (vertical direction, horizontal direction), lens distortion (radiation direction, tangential direction), and the like. The aberration information is configured as information (for example, table information) in which the identification information of each anterior eye camera 60 is associated with the correction coefficient corresponding thereto. The image correction unit 121 performs aberration correction on the captured image acquired by the anterior eye camera 60A or 60B by referring to the aberration information generated in this way. Such aberration correction is called calibration or the like.

(Feature position specifying unit 122)
The feature position specifying unit 122 analyzes each captured image acquired by the anterior eye camera 60 or each captured image whose distortion has been corrected by the image correcting unit 121, so that a predetermined feature portion of the anterior eye portion Ea is analyzed. A position (referred to as a feature position) in the captured image corresponding to is specified. For example, the center of the pupil of the eye E or the apex of the cornea is used as the predetermined characteristic part. Hereinafter, a specific example of the process of specifying the corneal apex will be described.

  The measurement optical system 30 is provided with an alignment index projection system (not shown). The alignment index projection system projects the alignment index light toward the cornea of the eye E under the control of the control unit 11 described later. The alignment index light beam projected by the alignment index projection system is reflected by the corneal surface and forms a bright spot-like virtual image (Purkinje image). The feature position specifying unit 122 specifies a bright spot image (bright spot area) in the anterior segment image of the eye E based on the distribution of pixel values (such as luminance values) of the captured image. In general, a bright spot image is drawn with higher brightness than other parts, so that a bright spot image can be specified by searching for a high brightness image area. At this time, the bright spot image may be specified in consideration of the shape of the bright spot area. In other words, the bright spot image can be specified by searching for a high-luminance image region having a substantially circular shape and a specific area.

  The feature position specifying unit 122 may obtain the center of gravity of the specified bright spot image (bright spot area), and may use this barycentric position as the corneal apex.

  Even when a feature position corresponding to another feature part such as a pupil is specified, the feature position can be specified based on the distribution of pixel values of the captured image in the same manner as described above.

(Three-dimensional position calculation unit 123)
The three-dimensional position calculation unit 123 is based on the positions of the two or more anterior segment cameras 60 and the feature positions (corneal vertex positions) in the two or more captured images specified by the feature position specifying unit 122. The three-dimensional position of the characteristic part of E is calculated. This process will be described with reference to FIG.

  FIG. 5 is a top view showing the positional relationship between the eye E and the anterior eye cameras 60A and 60B. The distance (base line length) between the two anterior eye cameras 60A and 60B is represented by “B”. A distance (imaging distance) between the baselines of the two anterior eye cameras 60A and 60B and the characteristic part P of the eye E is represented by “H”. The distance (screen distance) between each anterior eye camera 60A and 60B and the screen plane is represented by “f”.

  In such an arrangement state, the resolution of the image captured by the anterior eye cameras 60A and 60B is expressed by the following equation. Here, Δp represents pixel resolution.

Resolution in xy direction (planar resolution): Δxy = H × Δp / f
Resolution in the z direction (depth resolution): Δz = H × H × Δp / (B × f)

  The three-dimensional position calculation unit 123 has an arrangement relationship shown in FIG. 5 with respect to the positions (known) of the two anterior eye cameras 60A and 60B and the characteristic position corresponding to the characteristic part P in the two captured images. Is applied to calculate a three-dimensional position of the feature region P, that is, a three-dimensional position of the eye E to be examined. As described above, the three-dimensional position calculation unit 123 can calculate the three-dimensional position of the corneal apex of the eye E to be examined.

(Movement determination unit 124)
The movement amount determination unit 124 is based on the three-dimensional relative position between the optical unit 20 and the corneal apex (characteristic part P) obtained by the three-dimensional position calculation unit 123, and includes the movement amount (including the movement direction) of the optical unit 20. To decide. Specifically, the movement amount determination unit 124 determines the movement amount so that the position of the optical unit 20 with respect to the corneal apex position obtained by the three-dimensional position calculation unit 123 has a predetermined positional relationship. The predetermined positional relationship is such that the positions in the X direction and the Y direction coincide with the corneal apex position, and the distance in the Z direction becomes a predetermined working distance. The movement amount determined by the movement amount determination unit 124 is sent to the control unit 11. The control unit 11 performs control to change the position of the measurement optical system 30 by the calculated amount of movement starting from the current position of the measurement optical system 30. Accordingly, the first drive unit 80A and the second drive unit are set so that the optical axis of the measurement optical system 30 coincides with the axis of the eye E and the distance of the measurement optical system 30 with respect to the eye E becomes a predetermined working distance. At least one of 80B is controlled. Since the position of the Purkinje image differs depending on the corneal curvature, there is an error with respect to the corneal apex position, but by obtaining the corneal curvature with an average curvature radius of 8 mm, the error as a corneal shape measurement result is kept within an allowable range. be able to.

(Cornea shape information acquisition unit 125)
The corneal shape information acquisition unit 125 obtains corneal shape information of the eye E based on the captured image acquired by the anterior segment imaging system provided in the measurement optical system 30. The corneal shape information includes any of the parameter values described above.

  The corneal shape information acquisition unit 125 calculates the corneal curvature radius of the strong main meridian and the weak main meridian on the front surface of the cornea by analyzing the pattern image acquired by the anterior ocular segment imaging system, and based on the corneal curvature radius, A parameter representing the shape is calculated. For example, the corneal shape information acquisition unit 125 calculates a corneal curvature radius by performing arithmetic processing on the acquired pattern image, and calculates the corneal refractive power, the corneal astigmatism, and the corneal astigmatism axis angle from the calculated corneal curvature radius. Is calculated.

  Further, the corneal shape information acquisition unit 125 may obtain corneal shape information of the eye E based on at least one of the two captured images acquired by the anterior segment cameras 60A and 60B.

  The anterior segment imaging system provided in the anterior segment camera 60 (60A, 60B) or the measurement optical system 30 is an example of the “imaging unit” according to the embodiment. The kerato plate 40 is an example of an “optical member” according to the embodiment. The kerato plate 40 and the light source disposed on the back side of the kerato plate are examples of the “projection unit” according to the embodiment. The imaging lenses 61A, 61B, and 63A are examples of the “lens” according to the embodiment. The measurement optical system 30 is an example of an “optical system” according to the embodiment. The face support unit 70 is an example of a “support unit” according to the embodiment. At least one of the first drive unit 80A and the second drive unit 80B is an example of the “drive unit” according to the embodiment.

<Contrast with comparative example>
First, an ophthalmologic apparatus according to a comparative example of the embodiment will be described.

  FIG. 6 schematically shows a configuration of an optical system of an ophthalmologic apparatus according to a comparative example of the embodiment. FIG. 6 shows a kerato plate 40a according to a comparative example and an anterior eye camera 60a corresponding to the anterior eye camera 60A according to the embodiment. In FIG. 6, illustration of the anterior eye camera according to the comparative example corresponding to the anterior eye camera 60 </ b> B is omitted.

  The anterior eye camera 60a includes an imaging lens 61a and an imaging element 62a. When performing alignment using two or more captured images in an ophthalmic apparatus having a corneal shape measurement function, the kerato plate 40a is disposed in the imaging optical path. In this case, the kerato plate 40a is formed with a translucent part through which the imaging optical path of the anterior eye camera 60a passes. When the anterior segment camera 60a is simply arranged on the back side of the kerato plate 40a, the kerato plate 40a and the anterior segment camera 60a (imaging lens) are used to ensure a certain angle of view so as to ensure as wide a dynamic range as possible. The size R of the translucent part is determined from the positional relationship with 61a).

  FIG. 7 schematically shows the kerato plate 40a of FIG. FIG. 7 schematically shows a front view of the kerato plate 40a viewed from the eye E side.

  The kerato plate 40a is formed with an opening 41a through which the optical axis of the measurement optical system according to the comparative example passes and a ring-shaped diffuse transmission part 42a. Further, the kerato plate 40a is formed with a translucent part 43a through which the imaging optical path of the anterior eye camera 60a passes and a translucent part 44a through which the imaging optical path of the anterior eye camera 60b passes. In the comparative example, since the size R of the light transmitting parts 43a and 44a is required as described above, a part of the diffuse transmission part 42a overlaps with the light transmitting parts 43a and 44a. Therefore, a part of the measurement pattern projected on the cornea of the eye E is missing.

  FIG. 8 is an explanatory diagram of a measurement pattern projected onto the cornea of the eye E in the comparative example. FIG. 8 shows an image of the anterior segment Ea of the eye E to be examined in the comparative example.

  In the image IMG of the anterior segment shown in FIG. 8, a pattern image PT based on the reflected light of the measurement pattern light is drawn. The pattern image PT has defective portions LS1 and LS2. The deficient portion LS1 corresponds to the overlapping region of the diffuse transmission part 42a and the light transmission part 44a in the kerato plate 40a. The deficient portion LS2 corresponds to an overlapping region of the diffuse transmission part 42a and the light transmission part 43a in the kerato plate 40a. In this case, the measurement result of the corneal shape in the meridian range corresponding to the missing portions LS1 and LS2 cannot be obtained, and the required error of the corneal shape information becomes large.

  Next, the ophthalmologic apparatus 1 according to the embodiment will be described.

  FIG. 9 schematically shows the configuration of the optical system of the ophthalmologic apparatus 1 according to the embodiment. FIG. 9 shows the kerato plate 40 and the anterior eye camera 60A. 9, parts that are the same as those in FIG. 3 are given the same reference numerals, and descriptions thereof will be omitted as appropriate. In FIG. 9, the anterior eye camera 60B is not shown.

  In the embodiment, as described above, the entrance pupil of the anterior eye camera 60 is disposed at or near the light transmitting portion formed on the kerato plate 40. For example, as the imaging lens 61A, a lens system (for example, a high eye point lens) in which the entrance pupil is on the front side (incident side) of the lens surface can be used. The optical axis of the imaging lens 61A matches the direction of the photographing optical path of the anterior segment camera 60A. Thereby, it becomes possible to arrange the entrance pupil of the anterior eye camera 60 </ b> A at or near the light transmitting portion of the kerato plate 40. Therefore, even when the anterior eye camera 60A is arranged on the back side of the kerato plate 40, the size r1 (r <R) of the light transmitting part can be reduced while ensuring a sufficiently wide field of view.

  FIG. 10 schematically shows a kerato plate 40 according to the embodiment. FIG. 10 schematically shows a front view of the kerato plate 40 viewed from the eye E side.

  The kerato plate 40 is formed with an opening 41 through which the optical axis of the measurement optical system 30 passes and a ring-shaped diffuse transmission part 42. Further, the kerato plate 40 is formed with a translucent part 43 through which the imaging optical path of the anterior eye camera 60A passes and a translucent part 44 through which the imaging optical path of the anterior eye camera 60B passes. In the embodiment, since the size r1 of the light transmitting parts 43 and 44 is required as described above, the positions of the light transmitting parts 43 and 44 can be freely determined without overlapping the diffuse transmission part 42. Or even if it overlaps, a defective part can be suppressed to the minimum.

  For example, by forming the translucent portions 43 and 44 below the optical axis of the measurement optical system 30, the eyelids and eyelashes of the subject are reflected in the captured images acquired by the anterior eye cameras 60A and 60B. The possibility can be reduced. Moreover, even if the subject has a deep eye depression (orbit), anterior segment imaging can be suitably performed.

  Further, in the kerato plate 40, when a defect occurs in a part of the measurement pattern formed by transmitting the ring-shaped diffuse light transmitting portion 42 by the light transmitting portions 43 and 44 (that is, two or more light transmitting portions), It is desirable that the light transmitting parts 43 and 44 are formed at positions that are asymmetric with respect to the position corresponding to the optical axis of the measurement optical system 30 in the opening 41. When the translucent portions 43 and 44 are formed at point-symmetrical positions with respect to the position corresponding to the optical axis, depending on the distortion direction of the acquired pattern image, the major axis or minor axis when the pattern image is approximated to an ellipse Cannot be specified, and desired corneal shape information cannot be obtained. On the other hand, when the translucent portions 43 and 44 are formed at positions that are asymmetrical with respect to the position corresponding to the optical axis, at least the major axis and the minor axis are obtained by elliptically approximating the acquired pattern image. One of them can be specified, and more accurate corneal shape information can be obtained.

  FIG. 11 is an explanatory diagram of a measurement pattern projected onto the cornea of the eye E in the embodiment. FIG. 11 shows an image of the anterior segment Ea of the eye E to be examined in the embodiment.

  Also in the image IMG1 of the anterior segment shown in FIG. 11, a pattern image PT1 based on the reflected light of the measurement pattern light is drawn similarly to the image IMG shown in FIG. The pattern image PT1 has no missing portion, and the corneal shape information can be obtained accurately.

<Operation example>
Next, the operation of the ophthalmologic apparatus 1 will be described.

  FIG. 12 shows a flowchart of an operation example of the ophthalmologic apparatus 1 according to the embodiment. In FIG. 12, input of patient information (patient ID, patient name, etc.) of a subject, selection of an examination type (examination mode), and the like are performed in advance. Hereinafter, the case where the corneal shape information is obtained after the alignment operation will be mainly described.

(S1: Start projection of measurement pattern light and alignment index light)
The control unit 11 controls the light source disposed on the back side of the kerato plate 40 to output light from the light source. The light output from the light source is diffused and transmitted through the diffusing and transmitting part 42 shown in FIG. 10 and projected onto the anterior eye part Ea of the eye E as ring-shaped measurement pattern light. At the same time, the control unit 11 controls the alignment index projection system (not shown) to project the alignment index light beam onto the cornea of the eye E.

(S2: Start photographing the anterior segment)
Next, the control unit 11 (alignment control unit 111) controls the anterior segment cameras 60A and 60B to start photographing the anterior segment Ea.

  Each of the anterior eye cameras 60 </ b> A and 60 </ b> B repeats image acquisition at predetermined time intervals, and sequentially sends the acquired captured images to the alignment control unit 111. The alignment control unit 111 sequentially sends a pair of captured images acquired substantially simultaneously by the anterior eye cameras 60 </ b> A and 60 </ b> B to the data processing unit 12.

  The data processing unit 12 sequentially applies the following processing to a pair of captured images that are sequentially input. Although optional, the image correction unit 121 can correct distortion of the captured image based on the aberration information.

(S3: Specify bright spot image)
The alignment control unit 111 causes the feature position specifying unit 122 to specify the bright spot image in the anterior segment Ea by analyzing the pair of captured images acquired in step S2. For example, the feature position specifying unit 122 specifies an image region corresponding to the corneal reflection luminescent spot image of the eye E based on the pixel value of the captured image as described above, and the specified luminescent spot image. Specify the position of the center of gravity.

(S4: Specific success?)
The alignment control unit 111 determines whether or not a bright spot region is specified in step S3. The alignment control unit 111 determines the pupil region based on the luminance distribution of the anterior segment image acquired in step S2 and the area and shape of pixels exceeding the threshold in the anterior segment image identified in step S3. It can be determined whether or not is specified.

  When it is determined that the bright spot image has been identified (S4: Y), the operation of the ophthalmologic apparatus 1 proceeds to step S5. When it is determined that the bright spot image is not specified (S4: N), the operation of the ophthalmologic apparatus 1 proceeds to step S6.

(S5: Corneal vertex alignment)
When it is determined in step S4 that the bright spot image has been identified (S4: Y), the alignment control unit 111 switches the alignment mode to the corneal apex alignment mode. That is, the alignment control unit 111 causes the feature position specifying unit 122 to specify the position of the bright spot image from the image of the anterior segment Ea. The position of the bright spot image may be the barycentric position of the bright spot image obtained in step S3. Subsequently, the alignment control unit 111 causes the three-dimensional position calculation unit 123 to calculate the three-dimensional position of the pupil region using the positions of the bright spot images specified in the pair of captured images. The three-dimensional position calculation unit 123 determines a three-dimensional position (X coordinate value, Y coordinate value) of the pupil center of the eye E based on a pair of pupil region images (a pair of pupil centers) specified in the pair of captured images. , Z coordinate value).

  The alignment control unit 111 controls the first driving unit 80A so that the optical axis of the measurement optical system 30 (objective lens) is arranged at a position corresponding to the X coordinate value and the Y coordinate value of the obtained bright spot image. To do. Furthermore, the alignment control unit 111 controls the first driving unit 80A so that the measurement optical system 30 (objective lens) is arranged at a position corresponding to the Z coordinate value of the pupil center and a predetermined working distance (WD). To do. Specifically, the alignment control unit 111 causes the movement amount determination unit 124 to determine the movement amount of the measurement optical system 30 based on the three-dimensional relative position between the current position of the optical unit 20 and the corneal apex of the eye E to be examined. . The alignment control unit 111 controls the first drive unit 80 </ b> A so as to move the optical unit 20 based on the movement amount determined by the movement amount determination unit 124.

  When the pupil alignment is completed, the operation of the ophthalmologic apparatus 1 proceeds to step S7.

(S6: Manual alignment)
When it is determined in step S4 that no bright spot image has been specified (S4: N), the alignment control unit 111 switches the alignment mode to the manual alignment mode.

  In the manual alignment mode, the alignment control unit 111 receives an image of the anterior segment acquired by the anterior segment camera 60A and / or 60B (or an observation image of the anterior segment Ea acquired by the measurement optical system 30 or the like). And displayed as a moving image in real time on the display unit 91.

  The user operates the operation unit 92 to move the measurement optical system 30. At this time, the alignment control unit 111 controls the first drive unit 80 </ b> A according to the operation signal input from the operation unit 92. When manual alignment is completed, the operation of the ophthalmologic apparatus 1 proceeds to step S7.

(S7: Alignment complete?)
Until the alignment of step S5 or step S6 is completed (S7: N), step S3 to step S6 are repeatedly executed. This series of operations is repeated until, for example, the relative position of the corneal apex of the optical unit 20 and the eye E to be examined falls within a predetermined allowable range.

  When the alignment in step S5 or step S6 is completed (S7: Y), the operation of the ophthalmologic apparatus 1 proceeds to step S8.

(S8: Acquire pattern image)
When the alignment is completed (S7: Y), the control unit 11 analyzes the image of the anterior segment Ea acquired by the measurement optical system 30 after the alignment is completed, thereby reflecting the measurement pattern light projected on the cornea. A pattern image based on is acquired.

  In addition, since projection of the measurement pattern of step S1 should just be performed before step S8, the projection start of measurement pattern may be performed between step S7 and step S8.

(S9: Find corneal shape information)
The control unit 11 analyzes the pattern image acquired in step S8 and causes the corneal shape information acquisition unit 125 to calculate the corneal shape information of the eye E to be examined. The corneal shape information acquisition unit 125 calculates, for example, a corneal curvature radius by performing arithmetic processing on the acquired pattern image, and the corneal refractive power, the corneal astigmatism, and the corneal astigmatism axis angle from the calculated corneal curvature radius. Can be calculated. The control unit 11 can display the calculated corneal shape information on the display unit 91 or store it in the storage device. Thus, the operation of the ophthalmologic apparatus 1 ends (END).

  As described above, according to the embodiment, the position of the entrance pupil of the anterior eye camera 60 is arranged at or near the light transmitting parts 43 and 44 formed on the kerato plate 40. It is possible to provide an ophthalmologic apparatus in which the size (hole diameter) of 43 and 44 is reduced, the measurement pattern is not lost (or reduced), and alignment with a wide dynamic range is possible.

<Modification>
The configuration of the ophthalmologic apparatus according to the embodiment is not limited to the configuration illustrated in FIG. In the ophthalmologic apparatus according to the embodiment, a microlens may be used as the imaging lens of the anterior segment camera.

  Hereinafter, an ophthalmologic apparatus according to a modified example of the embodiment will be described focusing on differences from the ophthalmologic apparatus according to the embodiment. The configuration of the ophthalmologic apparatus according to the modification of the embodiment differs from the configuration of the ophthalmologic apparatus 1 according to the embodiment in the imaging lens of the anterior segment camera. A microlens is used as an imaging lens according to a modification. That is, at least one of the two or more anterior eye cameras 60 includes a corresponding translucent part or a microlens arranged in the vicinity thereof, and an imaging element arranged behind the microlens.

  FIG. 13 schematically shows a configuration of an optical system of an ophthalmologic apparatus according to a modified example of the embodiment. In FIG. 13, the same parts as those in FIG. FIG. 13 shows the kerato plate 40 and the anterior eye camera 60A. In FIG. 13, the anterior eye camera 60B is not shown.

  Also in this modification, the entrance pupil of the anterior segment camera 60 is arranged at or near the translucent portion formed on the kerato plate 40 as in the embodiment. In this modification, a microlens is used as the imaging lens 63A provided in place of the imaging lens 61A. The optical axis of the imaging lens 63A matches the direction of the photographing optical path of the anterior segment camera 60A. Thereby, it becomes possible to arrange the entrance pupil of the anterior eye camera 60 </ b> A at or near the light transmitting portion of the kerato plate 40. Therefore, even when the anterior eye camera 60A is arranged on the back side of the kerato plate 40, the size r2 (r <R) of the light transmitting part can be reduced while ensuring a sufficiently wide field of view.

  According to this modification, as in the embodiment, the position of the entrance pupil of the anterior segment camera 60 is arranged at or near the translucent portions 43 and 44 formed on the kerato plate 40. It is possible to provide an ophthalmologic apparatus in which the size (hole diameter) of the portions 43 and 44 can be reduced and alignment with a wide dynamic range can be performed.

  Instead of arranging the microlens at or near the translucent part formed on the kerato plate 40, a kerato plate in which a lens (for example, a Fresnel lens) is integrally molded at or near the translucent part is used. Also good.

<Effect>
The effect of the ophthalmologic apparatus according to the embodiment will be described.

  The ophthalmologic apparatus (1) according to the embodiment includes two or more imaging units (anterior eye cameras 60, 60A, 60B, imaging optical systems provided in the measurement optical system), and a projection unit (kerato plate 40 and kerato plate 40). A light source disposed on the back side of the corneal shape), a corneal shape information acquisition unit (125), and a movement amount determination unit (124). Two or more imaging parts image the anterior eye part (Ea) of the eye to be examined (E) substantially simultaneously from different directions. The projection unit is an optical member (kerato) in which a diffuse transmission part (42) having a predetermined pattern (ring-shaped pattern) and two or more light transmission parts (43, 44) through which the optical paths of two or more photographing parts pass are formed. The measurement pattern light obtained by diffusing and transmitting the light from the light source disposed on the back side of the optical member including the plate 40) is projected onto the anterior ocular segment. The corneal shape information acquisition unit obtains corneal shape information of the eye to be inspected based on the anterior eye image on which the measurement pattern light is projected by the projection unit. The movement amount determination unit determines the movement amount of the projection unit based on two or more captured images acquired by two or more imaging units. The entrance pupils of the two or more imaging units are arranged in the corresponding translucent part or in the vicinity thereof.

  According to such a configuration, since the positions of the entrance pupils of two or more photographing units are arranged at or near the light transmitting part formed on the optical member, the size (hole diameter) of the light transmitting part is reduced. However, it is possible to perform alignment with little or no pattern loss and a wide dynamic range. Thereby, an ophthalmologic apparatus capable of measuring a corneal shape with high accuracy can be provided.

  In the ophthalmologic apparatus according to the embodiment, at least one of the two or more imaging units includes a lens (imaging lens 61A) in which a front main plane is arranged in the vicinity of the corresponding translucent unit among the two or more translucent units. ) And an image sensor (62A) arranged on the rear side of the lens.

  According to such a configuration, using a lens (for example, a high eye point lens) in which the front main plane is disposed in the translucent part or in the vicinity thereof, the alignment range is wide, and a highly accurate corneal shape can be measured. An ophthalmic device can be provided.

  In the ophthalmologic apparatus according to the embodiment, at least one of the two or more imaging units includes a microlens (63A) disposed in or near a corresponding translucent unit among the two or more translucent units, and a microlens. And an imaging device (62A) arranged on the rear side.

  According to such a configuration, since a microlens can be used, it is possible to provide an ophthalmologic apparatus that can measure a corneal shape with high accuracy and a wide alignment range at low cost.

  In the ophthalmologic apparatus according to the embodiment, the two or more translucent parts include the opening (41), the optical axis passes through the opening, and the optical system (measurement optical system 30) acquires the data of the anterior eye part. ) May be included.

  According to such a configuration, the number of light transmitting portions formed on the optical member can be further reduced. Thereby, an ophthalmic apparatus capable of measuring a corneal shape with a wide alignment range and high accuracy can be easily provided.

  In the ophthalmologic apparatus according to the embodiment, the optical member is formed with the opening (41), and the optical system (measurement optical system 30) is arranged so that the optical axis passes through the opening and acquires the data of the anterior eye. The two or more translucent portions may be formed at positions that are asymmetric with respect to the position corresponding to the optical axis in the opening.

  According to such a configuration, even when there is a pattern defect due to the translucent part, it is possible to specify at least one of the major axis and the minor axis by approximating the acquired pattern image to an ellipse. Accurate corneal shape information can be acquired.

  Moreover, in the ophthalmologic apparatus which concerns on embodiment, the 2 or more translucent part may be formed below with respect to the optical axis.

  According to such a configuration, it is possible to reduce the possibility that the eyelids and eyelashes of the subject are reflected, or to appropriately acquire an image of the anterior segment even if the subject has a deep eye depression (orbit). It becomes possible to do.

  In addition, the ophthalmologic apparatus according to the embodiment includes a support unit (face support unit 70) that supports the face of the subject, and a drive unit (first drive unit 80A, first drive unit) that relatively moves between the optical system and the support unit. 2 drive unit 80B) and a control unit (11) for relatively moving the optical system and the support unit by controlling the drive unit based on the movement amount.

  According to such a configuration, it is possible to provide an ophthalmologic apparatus capable of auto-alignment with a wide alignment range and capable of measuring a corneal shape with high accuracy.

  Moreover, in the ophthalmologic apparatus which concerns on embodiment, the 2 or more translucent part may be formed in the position which does not overlap with a diffuse transmission part.

  According to such a configuration, it is possible to provide an ophthalmologic apparatus capable of measuring a corneal shape with a wide alignment range and high accuracy without causing a measurement pattern defect.

  In the ophthalmologic apparatus according to the embodiment, the predetermined pattern may be a ring pattern or a concentric pattern.

  According to such a configuration, it is possible to provide an ophthalmologic apparatus that has a wide alignment range and is capable of measuring a corneal shape with high accuracy by kerato measurement or platide measurement.

  The computer program for realizing the processing according to the embodiment can be stored in any recording medium readable by the computer. Examples of the recording medium include a semiconductor memory, an optical disk, a magneto-optical disk (CD-ROM / DVD-RAM / DVD-ROM / MO, etc.), a magnetic storage medium (hard disk / floppy (registered trademark) disk / ZIP, etc.), and the like. Can be used.

  It is also possible to send and receive computer programs via a network such as the Internet or a LAN.

  The aspects described above are merely examples for carrying out the present invention. A person who intends to implement the present invention can make arbitrary modifications (omission, replacement, addition, etc.) within the scope of the present invention.

DESCRIPTION OF SYMBOLS 1 Ophthalmology apparatus 11 Control part 111 Alignment control part 12 Data processing part 20 Optical unit 30 Measurement optical system 40, 40a Kerato board 41, 41a Opening part 42, 42a Diffuse transmission part 43, 43a, 44, 44a Translucent part 60, 60A , 60B Anterior eye camera 61, 61A, 63A Imaging lens 62, 62a Image sensor 80A First drive unit 80B Second drive unit 91 Display unit 92 Operation unit 121 Image correction unit 122 Feature position specifying unit 123 Three-dimensional position calculation unit 124 Movement amount determination unit 125 Corneal shape information acquisition unit E Eye to be examined Ea Anterior segment

Claims (9)

Two or more imaging units for imaging the anterior segment of the eye to be examined from substantially different directions at the same time;
Including an optical member on which a diffuse transmission part having a predetermined pattern and two or more light transmission parts through which optical paths of the two or more photographing parts pass are formed, and light from a light source disposed on the back side of the optical member A projection unit that projects the measurement pattern light obtained by diffusing and transmitting the diffuse transmission unit onto the anterior eye unit;
A corneal shape information acquisition unit for obtaining corneal shape information of the eye to be inspected based on an image of the anterior ocular segment onto which the measurement pattern light is projected by the projection unit;
A movement amount determination unit that determines a movement amount of the projection unit based on two or more captured images acquired by the two or more imaging units;
Including
Each of the entrance pupils of the two or more imaging units is an ophthalmologic apparatus disposed at a corresponding translucent unit or in the vicinity thereof. At least one of the two or more photographing units is
A lens in which a front principal plane is disposed in or near the corresponding translucent portion of the two or more translucent portions;
An image sensor disposed behind the lens;
The ophthalmic apparatus according to claim 1, comprising: At least one of the two or more photographing units is
A microlens disposed in or near the corresponding translucent portion of the two or more translucent portions;
An image sensor disposed behind the microlens;
The ophthalmic apparatus according to claim 1, comprising: The two or more light-transmitting portions include an opening,
The ophthalmologic apparatus according to any one of claims 1 to 3, further comprising an optical system in which an optical axis passes through the opening and acquires data of the anterior segment. An opening is formed in the optical member,
An optical system that is arranged so that an optical axis passes through the opening and acquires data of the anterior segment,
The two or more light-transmitting portions are formed at positions that are asymmetrical with respect to a position corresponding to the optical axis in the opening. An ophthalmic device according to claim 1. The ophthalmologic apparatus according to claim 5, wherein the two or more translucent portions are formed below the optical axis. A support part for supporting the face of the subject;
A drive unit that relatively moves the optical system and the support unit;
A control unit that relatively moves the optical system and the support unit by controlling the drive unit based on the movement amount;
The ophthalmologic apparatus according to any one of claims 4 to 6, wherein the ophthalmologic apparatus is included. The ophthalmologic apparatus according to any one of claims 1 to 7, wherein the two or more light-transmitting parts are formed at positions that do not overlap with the diffuse transmission part. The ophthalmic apparatus according to any one of claims 1 to 8, wherein the predetermined pattern is a ring pattern or a concentric pattern.

Images