JP6400313B2 - Shading plate and ophthalmic device - Google Patents

Description

  The present invention relates to a light shielding plate of an ophthalmologic apparatus.

  In the ophthalmic field, various devices are used for photographing and measurement. Examples of ophthalmologic apparatuses for photographing the fundus and anterior eye include an apparatus using optical coherence tomography (hereinafter referred to as OCT), a fundus camera, an SLO (Scanning Laser Ophthalmoscope), and a slit lamp. In addition, as an ophthalmologic apparatus for measuring the eye to be examined, an eye refraction examination apparatus (refractometer, keratometer), tonometer, and corneal characteristics (corneal thickness, cell distribution, etc.) for measuring the refractive characteristics of the eye to be examined. There are a specular microscope, a wavefront analyzer that obtains aberration information of an eye to be examined using a Hartmann-Shack sensor, and the like.

  In general, an ophthalmologic apparatus using an optical system is used in a dark room. This is to prevent external light from entering the eye of the subject and to prevent external light from entering the optical system. When external light is incident on the subject's eyes (including not only the subject eye but also the other eye), miosis occurs, which may interfere with imaging and measurement. Further, when external light is incident on the optical system, there is a possibility that the image quality of the photographed image is deteriorated and the accuracy and accuracy of the measurement result are lowered.

  Conventionally, depending on the scale of the medical institution and the usage state of the ophthalmic apparatus, there are cases where there is no dark room or it is difficult to prepare a dark room. In such a case, a negative curtain was used to prevent the adverse effect of external light.

  As described above, the black curtain is an effective means, but its installation work is complicated. For example, since the dark curtain is provided so as to cover most of the objective lens side of the ophthalmic apparatus and the front surface of the subject, a support portion having a size capable of hanging such a dark curtain is required. . It is very time-consuming to install such a support and hang a black curtain on it. Further, after the inspection is completed, it is necessary to remove the dark curtain and the support part.

  In order to solve such problems, a light shielding plate has been proposed (for example, Patent Document 1). The light shielding plate is provided so as to cover at least a peripheral portion of the eye to be examined. Since such a light-shielding plate is smaller than a dark curtain, it is easier to attach and detach than the dark curtain.

JP 2005-006870 A

  By the way, an eye opening operation may be performed in an ophthalmic examination. In the opening operation, the examiner keeps the eyelid of the eye to be opened using his / her finger or an opener. However, the conventional light shielding plate as in Patent Document 1 is configured without considering the opening operation. That is, the conventional light shielding plate is disposed close to the eye to be examined in order to block external light, and it has been difficult to secure a space for performing eye opening work by accessing the eye to be examined.

  An object of the present invention is to provide a light shielding plate capable of easily performing an opening operation while maintaining a function of shielding external light, and an ophthalmologic apparatus including the light shielding plate.

The invention according to claim 1 for solving the above problem is a light shielding plate for preventing external light from entering the eye of the subject and the optical system of the ophthalmic apparatus, and is mounted on the ophthalmic apparatus. And at least a portion around the subject eye of the subject's face in a state of being attached to the ophthalmologic apparatus via the attachment portion, and the subject's eye or its surroundings And a plate-like light-shielding portion that can be deformed by receiving an external force at least at the upper edge and / or the side edge.
The invention concerning Claim 2 for solving said subject is the light-shielding plate of Claim 1, Comprising: The upper end edge of the said light-shielding part is formed in concave shape, It is characterized by the above-mentioned.
The invention concerning Claim 3 for solving said subject is the light-shielding plate of Claim 1 or 2, Comprising: The lower end edge of the said light-shielding part is formed in concave shape, It is characterized by the above-mentioned.
The invention according to claim 4 for solving the above problem is the light shielding plate according to any one of claims 1 to 3, wherein the deformable portion of the light shielding portion is a flexible material. It is formed by these.
The invention concerning Claim 5 for solving said subject is the light-shielding plate of Claim 4, Comprising: The said material is an elastic material, It is characterized by the above-mentioned.
The invention concerning Claim 6 for solving said subject is a light-shielding plate in any one of Claims 1-5, Comprising: For cutting out the predetermined part containing a part of lower end edge of the said light-shielding part A guide wire is provided.
The invention according to claim 7 for solving the above-described problem is the light shielding plate according to claim 6, wherein the guide line is formed thinner than other portions in the light shielding portion. And
The invention according to claim 8 for solving the above problem is the light-shielding plate according to claim 6 or 7, which can be attached to the first ophthalmic apparatus and the second ophthalmic apparatus having different appearance shapes. The lower end edge has a shape that follows the external shape of the first ophthalmic apparatus, and the lower end edge after the predetermined portion is cut has a shape that follows the external shape of the second ophthalmic apparatus. It is characterized by that.
The invention concerning Claim 9 for solving said subject is the light-shielding plate in any one of Claims 1-8, Comprising: The surface facing the said subject's face in the said light-shielding part is concave shape. It is characterized by being formed.
The invention concerning Claim 10 for solving said subject is the light-shielding plate in any one of Claims 1-9, Comprising: The surface facing the said subject's face in the said light-shielding part is black. It is characterized by being.
The invention concerning Claim 11 for solving said subject is the light-shielding plate in any one of Claims 1-10, Comprising: The area | region of the lower edge part side of the said light-shielding part consists of several notches. It is formed in a strip shape.
An invention according to claim 12 for solving the above-mentioned problem is an ophthalmologic apparatus having an optical system, a subject's eye, and a light-shielding plate for preventing external light from entering the optical system. The light shielding plate is opposed to at least a portion around the subject's eye in the face of the subject in a state of being attached to the ophthalmologic device via the attachment portion and an attachment portion for attaching to the ophthalmic device. And a plate-shaped light-shielding portion that is arranged and at least an upper edge portion and / or a side edge portion can be deformed by receiving an external force when accessing the eye of the subject or the periphery thereof.
A thirteenth aspect of the invention for solving the above problem is the ophthalmic apparatus according to the twelfth aspect of the present invention, wherein a movable arm having a base end attached to the main body of the ophthalmic apparatus, and a distal end portion of the movable arm are provided. An external fixation target for fixing the eye to be examined in a direction outside the optical path of the optical system, and the upper edge of the light shielding plate is a movable arm of the movable arm. It is formed in a concave shape so as not to interfere with at least a part of the range.

  According to the light shielding plate of the present invention, it is possible to easily perform the opening operation while maintaining the function of shielding external light.

The schematic perspective view which shows the structure of the light-shielding plate concerning 1st Embodiment. The schematic plan view which shows the structure of the light-shielding plate concerning 1st Embodiment. The schematic front view which shows the structure of the light-shielding plate concerning 1st Embodiment. The schematic bottom view which shows the structure of the light-shielding plate concerning 1st Embodiment. The schematic back view which shows the structure of the light-shielding plate concerning 1st Embodiment. The schematic left view which shows the structure of the light-shielding plate concerning 1st Embodiment. The schematic perspective view which looked at the light-shielding plate and the ophthalmologic apparatus from the front left side. The schematic perspective view which looked at the light-shielding plate and the ophthalmologic apparatus from the left rear side. The schematic perspective view which looked at the light-shielding plate and the ophthalmologic apparatus from the left front side. The schematic perspective view which shows the connection structure of the light-shielding plate and ophthalmic apparatus through a connection member. The schematic perspective view which shows the structure of a connection member. Schematic showing an example of a structure of the ophthalmologic apparatus which concerns on embodiment. Schematic showing an example of a structure of the ophthalmologic apparatus which concerns on embodiment. The schematic block diagram showing an example of the composition of the ophthalmologic apparatus concerning an embodiment. The schematic front view which shows the structure of the light-shielding plate concerning a modification. The schematic perspective view which shows the structure of the light-shielding plate concerning 2nd Embodiment. The schematic perspective view of the light-shielding plate and ophthalmic apparatus concerning 2nd Embodiment. The schematic perspective view of the light-shielding plate and ophthalmic apparatus concerning 2nd Embodiment.

  The ophthalmologic apparatus 1 and the light shielding plate 100 according to the embodiment will be described with reference to FIGS. The light shielding plate 100 is a member for shielding external light from entering the optical system of the ophthalmologic apparatus 1. Therefore, it is desirable that the relative position of the light shielding plate 100 with respect to the subject is maintained at the time of inspection. Therefore, the light shielding plate 100 has such a rigidity that it can maintain its posture or shape while being supported by a support member (for example, the connection member 200). Furthermore, the size of the light shielding plate 100 for blocking the incidence of external light to the optical system is such that, for example, the forehead and the side and upper side of the eye to be examined are covered in the body width direction of the subject relative to the ophthalmologic apparatus 1. is there. Moreover, the light-shielding plate 100 has the flexibility which can deform | transform by receiving external force so that it may demonstrate below. Further, the light shielding plate 100 has elasticity for returning from the deformed state to the original shape when the external force is no longer applied after receiving the external force.

  In the description of the light shielding plate 100 according to the embodiment, the directions of “front”, “rear”, “left”, “right”, “upper”, and “lower” are defined based on the ophthalmologic apparatus 1. As an example, the direction from the lens barrel 1a of the objective lens of the ophthalmologic apparatus 1 (see FIG. 7 and the like) toward the eye to be examined is defined as “front” and the opposite direction is defined as “rear”. Further, the installation surface side of the ophthalmologic apparatus 1 is defined as “downward” and the opposite direction is defined as “upward”. In the following description, “left” and “right” are defined based on the above “front”, “rear”, “upper”, and “lower”. Further, in the installed ophthalmologic apparatus 1, the front surface may be described as “front” and the back surface may be described as “back”.

  Further, in the state in which the light shielding plate 100 is connected to the ophthalmic apparatus 1, the directions of “front”, “rear”, “left”, “right”, “upper”, and “lower” with respect to the light shielding plate 100 This is the same as each direction in the apparatus 1.

[First Embodiment]
(Shading plate)
<Overview>
The overall configuration of the light shielding plate 100 according to the embodiment will be described with reference to FIGS.

  FIGS. 1-6 shows schematic structure of the light-shielding plate 100 concerning 1st Embodiment. FIG. 1 is a schematic perspective view. FIG. 2 is a schematic plan (top) view. FIG. 3 is a schematic front view. FIG. 4 is a schematic bottom view. FIG. 5 is a schematic rear view. FIG. 6 is a schematic left side view.

  As shown in FIGS. 1 and 2, the light shielding plate 100 is formed in a curved plate shape that is convex on the back side. In the light shielding plate 100 illustrated in FIG. 2, the intermediate position in the left-right direction protrudes most to the rear side. Moreover, in the example shown in FIGS. 2-5, the light-shielding plate 100 has the shape of right-and-left object. In addition, since the light-shielding plate 100 should just cover at least the subject's eye and its circumference | surroundings, it does not necessarily need to be a curved plate shape. For example, it may be flat. In the case of a flat plate shape, the left and right sides of the light shielding plate 100 may be refracted toward the subject. The light shielding plate 100 corresponds to an example of a “light shielding portion”.

  3 and 5, in the light shielding plate 100, the left-right direction corresponds to the longitudinal direction, and the up-down direction corresponds to the short direction. The thickness of the light shielding plate 100 is set in consideration of the balance between the rigidity for maintaining the posture of the light shielding plate 100 and the flexibility that can be deformed when subjected to an external force. For example, if the light shielding plate 100 is too thick, flexibility is reduced and deformation becomes difficult. On the other hand, if the light shielding plate 100 is made too thin, the rigidity is reduced and it is difficult to maintain the posture of the light shielding plate 100. Therefore, the thickness of the light shielding plate 100 is set in consideration of rigidity and flexibility according to the material constituting the light shielding plate 100. The material constituting the light shielding plate 100 will be described later.

  The light shielding plate 100 is preferably formed of a material that has as low a light reflectance as possible and absorbs light in the widest possible wavelength band. Therefore, at least the front side (subject side) surface (front side) of the light shielding plate 100 is black, for example.

  Further, connection portions 101 a and 101 b are provided on the back surface of the light shielding plate 100. The connection portions 101 a and 101 b are for connecting the light shielding plate 100 to the ophthalmologic apparatus 1. These connecting portions 101a and 101b will be described later with reference to FIGS. The light shielding plate 100 and the connecting portions 101a and 101b constitute an example of a “light shielding plate”.

  As shown in FIGS. 2 to 5, a part of an upper portion (hereinafter referred to as “upper edge”; the two-dot chain line portion in FIG. 3) of the peripheral edge of the light shielding plate 100 is partially in the center of the light shielding plate 100. It is formed in a concave shape that is recessed toward the side. This concave portion will be described later as a first concave portion 103 with reference to FIGS.

  Further, the lower part of the peripheral edge of the light shielding plate 100 (the one-dot chain line part in FIG. 3; hereinafter referred to as “lower edge”) is formed in a concave shape in which most of the lower part is recessed toward the upper edge of the light shielding plate 100. Has been. This portion will be described later as a second recess 105 with reference to FIGS. 3 to 5, the shape of the second concave portion 105 indicated by a dotted line is adapted to the contour shape of the housing of the ophthalmologic apparatus 1 as described later, and is limited to the shape shown in these drawings. Absent.

  In the following description, when “end edge” is described, it indicates an outline portion when the light shielding plate 100 is viewed from the front or the back. Therefore, the upper end edge indicates a portion located on the upper side of the contour portion, and the lower end edge indicates a portion located on the lower side. On the other hand, when “edge” is described, it includes “edge” and the surrounding area. Therefore, the upper edge portion indicates the upper end edge and its vicinity region, and the lower edge portion indicates the lower end edge and its vicinity region. The same applies to the side edges and side edges.

<Connection unit 101a, Connection unit 101b>
As shown in FIGS. 1, 2, 4 to 6, connection portions 101 a and 101 b are provided at a predetermined interval on the back surface of the light shielding plate 100 curved backward. As shown in FIGS. 5 and 6, the connecting portions 101a and 101b are formed in a cylindrical shape protruding rearward. As will be described later, the engaging portion 203a of the connecting member 200 is inserted into the connecting portion 101a, and the engaging portion 203b of the connecting member 200 is inserted into the connecting portion 101b (see FIGS. 7 to 9). .

  In the example shown in FIG. 5, the connecting portions 101 a and 101 b are formed at positions equally spaced in the width direction from the center position in the width direction (left and right direction) of the light shielding plate 100. In FIG. 5, the distance from the connection part 101a to the connection part 101b and the distance from the connection part 101a to the left end of the light shielding plate 100 are substantially equal. Further, the distance from the connecting portion 101b to the connecting portion 101a is substantially equal to the distance from the connecting portion 101b to the right end of the light shielding plate 100. In other words, the connecting portions 101a and 101b are provided at positions where the light-shielding plate 100 is approximately divided into three equal parts in the left-right direction (positions of three equal points). In FIG. 5, the connecting portions 101 a and 101 b are provided at approximately the same height position (a position corresponding approximately in the vertical direction of the light shielding plate 100). Further, the connection part 101 a and the connection part 101 b are provided above the center of the light shielding plate 100.

  The connection units 101a and 101b correspond to an example of “mounting unit”. Or the combination of the connection parts 101a and 101b and the connection member 200 corresponds to an example of the “mounting part”.

<First recess 103>
As shown in FIG. 3, the lowest position of the first recess 103 recessed downward is arranged in the middle in the left-right direction. The first concave portion 103 has a predetermined length from the lowest position in the left and right directions, and gradually becomes shallower (shorter in the vertical direction) as it goes in the left direction and the right direction. Have. In other words, the first recess 103 is formed so as to smoothly go upward from the lowest position in the left and right directions.

  The depth of the first recess 103 is set according to the movable range of the external fixation target 9 (see FIG. 8) provided in the ophthalmologic apparatus, for example. In the examples shown in FIGS. 2 to 5, the length of the first recess 103 in the left-right direction is about 2/3 of the width of the light shielding plate 100. The length in the left-right direction of the light shielding plate 100 is, for example, slightly longer than the length in the left-right direction of the forehead pad 5 described later (see FIG. 7).

  Depending on the ophthalmologic apparatus, an external fixation target 9 is provided on the front side of the objective lens. The external fixation target 9 has a movable arm. The base end of the movable arm is attached to the face holding means (forehead pad 5 or chin rest 7 or the like) or the housing of the ophthalmic apparatus 1. A fixation lamp is provided at the tip of the movable arm. The examiner can place the fixation lamp at a desired position by operating the movable arm. As a result, the eye to be examined can be fixed in any direction outside the optical path of the optical system of the ophthalmologic apparatus 1. Depending on the size and shape of the conventional light-shielding plate, the light-shielding plate may come into contact with the movable arm or the fixation lamp of the external fixation target 9, and the operation of the external fixation target 9 may be hindered. In this respect, the light shielding plate 100 of the present embodiment is provided with the first concave portion 103 in consideration of the movable range of the external fixation target 9, thereby preventing interference between the external fixation target 9 and the light shielding plate 100. Is possible.

<Second recess 105>
When the light shielding plate 100 is connected to the ophthalmologic apparatus 1 in one example, the lower edge portion thereof is arranged so that no external light enters by making no gap between the ophthalmic apparatus 1. In one example, the light shielding plate 100 has a lower edge contacting or approaching the housing of the ophthalmic apparatus 1. Accordingly, the second recess 105 provided in the lower edge portion of the light shielding plate 100 has an outer shape of the ophthalmologic apparatus 1 (for example, the lens barrel) such as the lens barrel 1a of the objective lens so that a gap is not generated between the second recess 105 and the ophthalmologic apparatus 1. It is formed in accordance with 1a). Hereinafter, an example of the shape of the second recess 105 will be described with reference to FIG.

  The second recess 105 includes an intermediate portion 105a and a first side portion 105b and a second side portion 105c formed on one end side and the other end side of the intermediate portion 105a, respectively. The intermediate portion 105 a has a concave shape that forms a symmetrical arc that is recessed toward the approximate center of the light shielding plate 100. The first side portion 105 b is formed so as to be recessed from the predetermined position (left end side) on the left side of the lower edge portion of the light shielding plate 100 toward the upper edge side of the light shielding plate 100. The first side portion 105b extends horizontally by a predetermined distance toward the right side, and is adjacent to the intermediate portion 105a at the right end.

  In the example of FIG. 3, the most depressed position (on the upper edge side) of the intermediate portion 105 a corresponds to the intermediate position in the left-right direction of the light shielding plate 100. The second concave portion 105 is formed so that the first concave portion 103 gradually goes downward from this position toward the first side portion 105b and the second side portion 105c.

  The right end of the intermediate portion 105a is adjacent to the second side portion 105c. The second side portion 105c has a shape in which the first side portion 105b is symmetrical. In the example shown in FIG. 3, the entire second recess 105 is formed to be symmetric with respect to the bottom (intermediate position) of the intermediate portion 105 a.

<Material>
In order to satisfy the above-described conditions regarding rigidity, flexibility, and elasticity, for example, a rubber material having a hardness of about 60 to 70 in international rubber hardness (IRHD: International Rubber Hardness Degree) is used as the light shielding plate 100. As the rubber material, for example, silicone rubber is used.

  When silicone rubber is used, the shading plate 100 is difficult to break due to its toughness. Further, due to the chemical resistance of silicone rubber, for example, the light shielding plate 100 can be cleaned with alcohol or the like. Moreover, you may provide the material which has antibacterial property and antifouling property. Further, the light shielding plate 100 made of such a material is effective in that the connection portion 101a and the connection portion 101b of the light shielding plate 100 are not easily detached from the engagement portion 203a and the engagement portion 203b of the connection member 200. is there.

(Connection of ophthalmic device and light shielding plate)
Next, a configuration for connecting the light shielding plate 100 according to the first embodiment to the ophthalmologic apparatus 1 will be described with reference to FIGS.

  7 to 9 show the ophthalmologic apparatus 1 in a state where the light shielding plate 100 is connected. FIG. 7 is a schematic perspective view of the ophthalmologic apparatus 1 viewed from the front left side. FIG. 8 is a schematic perspective view of the ophthalmologic apparatus 1 viewed from the left rear side. FIG. 9 is a schematic perspective view of the ophthalmologic apparatus 1 viewed from the left front side. FIG. 10 is a schematic perspective view showing an outline of a connection configuration between the light shielding plate 100 and the ophthalmologic apparatus 1 via the connection member 200. FIG. 11 is a schematic perspective view showing a schematic configuration of the connection member 200. 9 and 10, illustration of the forehead rest 5, the chin rest 7 and the like is omitted.

<Ophthalmic device front>
As shown in FIGS. 7 and 8, an objective lens barrel 1 a, a forehead support 5, and a chin rest 7 are provided on the front side of the ophthalmic apparatus 1. The lens barrel 1 a is provided in front of the main body of the ophthalmologic apparatus 1. The forehead pad 5 is provided slightly in front of the lens barrel 1a. The forehead rest 5 has a proximal end on the lower end side in front of the main body of the ophthalmic apparatus 1. The forehead pad 5 has a frame holding portion protruding above the base end and a frame body provided at the upper end of the frame holding portion and opening in the front-rear direction of the ophthalmologic apparatus 1. The forehead of the subject is in contact with the front of the upper edge of the frame of the forehead pad 5. A chin rest 7 on which the subject's chin is placed is provided at the lower edge of the frame. As shown in FIG. 7, when the frame body of the forehead pad 5 is faced from the front side, the lens barrel 1a is located at a position between the upper edge portion and the lower edge portion of the frame body and a position slightly behind the frame body. Each part is provided so that can be seen.

<Position of light shielding plate 100>
As shown in FIGS. 7-9, the light-shielding plate 100 is arrange | positioned so that it may be mounted in the back of the front end of the lens-barrel 1a and on the housing | casing holding the lens-barrel 1a. As described above, the second recess 105 corresponding to the lower edge of the light shielding plate 100 has a shape that matches the outer shape of the light shielding plate 100. Therefore, the light shielding plate 100 is disposed so that there is almost no gap between the housing of the ophthalmologic apparatus 1.

  Further, since the light shielding plate 100 is arranged so that the lower end edge thereof is along the peripheral surface of the lens barrel 1a, the portion around the eye to be examined facing the objective lens (lens barrel 1a) is covered with the light shielding plate 100. Further, since the light shielding plate 100 has the same width as the forehead pad 5, the other eye of the subject is covered with the light shielding plate 100.

<Connecting member 200>
As shown in FIGS. 8 to 10, the light shielding plate 100 and the ophthalmologic apparatus 1 are detachably connected via a connecting member 200. That is, the connection member 200 functions as an attachment of the light shielding plate 100. The shape of the connecting member 200 is not limited to the illustrated shape, but may be a shape as shown in FIG. 8 or FIG. Hereinafter, an example of the connection member 200 illustrated in FIG. 11 will be described.

  As shown in FIG. 11, the connection member 200 includes a main body portion 201 and a pair of engaging portions 203a and 203b. The main body 201 includes a holding part 201a that holds the engaging parts 203a and 203b, and a pair of leg parts 201b and 201c that extend downward from the lower edge of the holding part 201a. The engaging portions 203a and 203b protrude forward from the front surface of the flat plate-shaped holding portion 201a, and are disposed at positions that are equal to the left and right with respect to the vertical center line of the holding portion 201a. The distal end portions of the engaging portions 203a and 203b are formed to have a larger diameter than the shaft portion.

  The distal ends of the engaging portions 203a and 203b are formed in a spherical shape having a larger diameter than the shaft portion. The engaging portion 203a is formed in a size that can be inserted into the cylindrical connecting portion 101a as a whole. The diameter of the spherical portion of the protruding end is formed larger than the diameter inside the connecting portion 101a. Since the connecting portion 101a is integral with the light shielding plate 100 and is made of an elastic material, the engaging portion 203a is pushed into the connecting portion 101a to engage the elastic connecting portion 101a having a cylindrical shape. The spherical portion of the portion 203a enters the far side of the connecting portion 101a while expanding.

  When the engaging portion 203a is inserted into the connecting portion 101a, the engaging portion 203a is connected to the connecting portion by the frictional force between the spherical portion of the engaging portion 203a and the inner peripheral surface of the connecting portion 101a due to the elasticity of the connecting portion 101a. 101a. Since the engaging portion 203b has the same configuration as the engaging portion 203a and the connecting portion 101b has the same configuration as the connecting portion 101a, the engaging portion 203b is also held in the connecting portion 101b. The connection member 200 is held on the light shielding plate 100 by such engagement between the connection portion 101a and the engagement portion 203a and engagement between the connection portion 101b and the engagement portion 203b. Thereby, the state shown in FIG. 10 is changed to the state shown in FIG.

  As shown in FIG. 8, the leg parts 201b and 201c of the connecting member 200 protrude in parallel from the flat holding part 201a, and the tip part is refracted forward. The bent portions at the tips of the leg portions 201b and 201c are brought into contact with the back surface of the light shielding plate 100 and contribute to maintaining the posture of the light shielding plate 100. That is, the connecting member 200 contributes to maintaining the posture by supporting the light shielding plate 100 at four points by the engaging portions 203a and 203b and the leg portions 201b and 201c. In addition, the pair of legs 201b and 201c sandwich the lens barrel 1a, and the connection member 200 and the ophthalmologic apparatus 1 are connected by screws, adhesives, hook-and-loop fasteners (not shown) provided separately. As a result, the light shielding plate 100 is attached to the ophthalmic apparatus 1.

  As described above, when the light shielding plate 100 is connected to the connection member 200 and the connection member 200 is connected to the ophthalmic apparatus 1, the light shielding plate 100 is connected to the ophthalmic apparatus 1.

  The light shielding plate 100 described above has a shape that covers the periphery of the subject of the ophthalmologic apparatus 1, and the length (width) in the left-right direction is slightly longer than the forehead 5 and the length in the up-down direction is in the left-right direction. It is about 2/3 of the length. As described above, since the light shielding plate 100 is sufficiently small as compared with the conventional black curtain, the attaching operation to the ophthalmologic apparatus 1 is easy. Therefore, the work efficiency concerning inspection improves. Further, since the light shielding plate 100 is configured to contact the ophthalmologic apparatus 1 without a gap, the outside of the eye of the subject or the optical system of the ophthalmologic apparatus 1 can be obtained without increasing the size of the light shielding plate 100. It is possible to appropriately prevent the incidence of light.

  In addition, since the surface of the light shielding plate 100 on the subject side is black, reflection of external light on the front surface of the light shielding plate 100 is suppressed, and external light is reflected to the subject side through the light shielding plate 100. It is possible to prevent this. As a result, miosis and intrusion of external light into the optical system of the ophthalmic apparatus 1 can be avoided. Therefore, the possibility of hindering shooting and measurement is reduced.

  Further, the light shielding plate 100 has such a rigidity that it can maintain its posture or shape while being supported by the connection member 200. Further, the light shielding plate 100 has flexibility that can be deformed by receiving an external force. Therefore, a person who examines the subject with the ophthalmologic apparatus 1 can access the subject's eye and its surroundings by bending and bending the light shielding plate 100.

  As described above, according to the light shielding plate 100 of the present embodiment, it is possible to facilitate access to the eye to be inspected during eye opening work while sufficiently exhibiting the function of blocking the external light by connecting to the ophthalmologic apparatus 1. it can. Further, since the light shielding plate 100 has elasticity, the light shielding plate 100 returns to the original shape from the deformed state when the access to the eye to be examined is completed, that is, when the application of force to the light shielding plate 100 is released.

(Ophthalmic equipment)
An example of an embodiment of an ophthalmologic apparatus will be described in detail with reference to the drawings. As an example, the ophthalmologic apparatus of the present embodiment forms a tomographic image or a three-dimensional image of the eye to be examined using OCT. In this specification, images acquired by OCT may be collectively referred to as OCT images. In addition, a measurement operation for forming an OCT image may be referred to as OCT measurement. In addition, it is possible to use suitably the description content of the literature described in this specification as the content of the following embodiment.

  In the following embodiment, a configuration to which Fourier domain type OCT is applied will be described in detail. The ophthalmologic apparatus according to the embodiment can acquire an OCT image of the fundus using a spectral domain OCT technique, and can acquire a fundus image and an anterior ocular segment image. Note that the configuration according to the present invention can be applied to an ophthalmologic apparatus using a method other than the spectral domain, for example, a swept source OCT or an infath OCT technique.

  In this embodiment, an apparatus in which an OCT apparatus and a fundus camera are combined will be described. However, an ophthalmic imaging apparatus other than the fundus camera, for example, an SLO, a slit lamp, or an ophthalmic surgical microscope can be combined with the OCT apparatus. is there. In addition, the configuration according to this embodiment can be incorporated into a single OCT apparatus.

  The ophthalmologic apparatus 1 includes a fundus camera, an SLO, a slit lamp, an eye refraction examination apparatus (refractometer, keratometer), a tonometer, a specular microscope for obtaining corneal characteristics (corneal thickness, cell distribution, etc.), and a Hartmann-Shack sensor. A wavefront analyzer or the like that obtains aberration information of the eye to be inspected by using a lens.

[Constitution]
As shown in FIGS. 12 and 13, the ophthalmologic apparatus 1 includes a fundus camera unit 2, an OCT unit 1000, and an arithmetic control unit 2000. The retinal camera unit 2 has almost the same optical system as a conventional retinal camera. The OCT unit 1000 is provided with an optical system for acquiring an OCT image of the fundus. The arithmetic control unit 2000 includes a computer that executes various arithmetic processes and control processes.

[Fundus camera unit]
The fundus camera unit 2 shown in FIG. 12 is provided with an optical system for acquiring a two-dimensional image (fundus image) representing the surface form of the fundus oculi Ef of the eye E to be examined. The fundus image includes an observation image and a captured image. The observation image is, for example, a monochrome moving image formed at a predetermined frame rate using near infrared light. In addition, when the optical system is focused on the anterior segment Ea of the eye E, the fundus camera unit 2 can obtain an observation image of the anterior segment Ea. The captured image may be, for example, a color image obtained by flashing visible light, or a monochrome still image using near infrared light or visible light as illumination light. The fundus camera unit 2 may be configured to be able to acquire images other than these, such as a fluorescein fluorescent image, an indocyanine green fluorescent image, a spontaneous fluorescent image, and the like.

  The fundus camera unit 2 is provided with a chin rest 7 and a forehead support 5 for supporting the face of the subject. The fundus camera unit 2 is provided with an illumination optical system 10 and a photographing optical system 30. The illumination optical system 10 irradiates the fundus oculi Ef with illumination light. The photographing optical system 30 guides the fundus reflection light of the illumination light to an imaging device (CCD image sensor (sometimes simply referred to as a CCD) 35, 38). The imaging optical system 30 guides the signal light from the OCT unit 1000 to the fundus oculi Ef and guides the signal light passing through the fundus oculi Ef to the OCT unit 1000.

  The observation light source 11 of the illumination optical system 10 is constituted by a halogen lamp, for example. The light (observation illumination light) output from the observation light source 11 is reflected by the reflection mirror 12 having a curved reflection surface, passes through the condensing lens 13, passes through the visible cut filter 14, and is converted into near infrared light. Become. Further, the observation illumination light is once converged in the vicinity of the photographing light source 15, reflected by the mirror 16, and passes through the relay lenses 17 and 18, the diaphragm 19 and the relay lens 20. Then, the observation illumination light is reflected at the peripheral portion (region around the hole portion) of the aperture mirror 21, passes through the dichroic mirror 46, and is refracted by the objective lens 22 to illuminate the fundus oculi Ef. An LED (Light Emitting Diode) can also be used as the observation light source.

  The fundus reflection light of the observation illumination light is refracted by the objective lens 22, passes through the dichroic mirror 46, passes through the hole formed in the central region of the perforated mirror 21, passes through the dichroic mirror 55, and is a focusing lens. It is reflected by the mirror 32 via 31. Furthermore, the fundus reflection light passes through the half mirror 39A, is reflected by the dichroic mirror 33, and forms an image on the light receiving surface of the CCD image sensor 35 by the condenser lens. The CCD image sensor 35 detects fundus reflected light at a predetermined frame rate, for example. On the display device 3, an image (observation image) based on fundus reflection light detected by the CCD image sensor 35 is displayed. Note that, when the photographing optical system 30 is focused on the anterior segment Ea, an observation image of the anterior segment Ea of the eye E is displayed.

  The imaging light source 15 is constituted by, for example, a xenon lamp. The light (imaging illumination light) output from the imaging light source 15 is applied to the fundus oculi Ef through the same path as the observation illumination light. The fundus reflection light of the imaging illumination light is guided to the dichroic mirror 33 through the same path as that of the observation illumination light, passes through the dichroic mirror 33, is reflected by the mirror 36, and is reflected by the condenser lens 37 of the CCD image sensor 38. An image is formed on the light receiving surface. On the display device 3, an image (captured image) based on fundus reflection light detected by the CCD image sensor 38 is displayed. Note that the display device 3 that displays the observation image and the display device 3 that displays the captured image may be the same or different. In addition, when similar imaging is performed by illuminating the eye E with infrared light, an infrared captured image is displayed. It is also possible to use an LED as a photographing light source.

  The illumination optical system 10 has a small pupil stop that can be inserted into and removed from the optical path. The small pupil stop is inserted into the optical path when the eye E is a small pupil eye. The small pupil stop is arranged in the optical path as a stop 19, for example. When the pupil diameter of the eye E is normal, an aperture (normal pupil aperture) that is applied to the imaging of the eye E with the normal pupil diameter is disposed as an aperture 19 in the optical path. That is, the stop 19 includes a normal pupil stop and a small pupil stop that can alternatively be arranged in the optical path.

  An LCD (Liquid Crystal Display) 39 displays a fixation target and an eyesight measurement index. The fixation target is an index for fixing the eye E to be examined, and is used at the time of fundus photographing or OCT measurement.

  A part of the light output from the LCD 39 is reflected by the half mirror 39A, reflected by the mirror 32, passes through the focusing lens 31 and the dichroic mirror 55, passes through the hole of the perforated mirror 21, and reaches the dichroic. The light passes through the mirror 46, is refracted by the objective lens 22, and is projected onto the fundus oculi Ef.

  By changing the display position of the fixation target on the screen of the LCD 39, the fixation position of the eye E can be changed. As the fixation position of the eye E, for example, a position for acquiring an image centered on the macular portion of the fundus oculi Ef, or a position for acquiring an image centered on the optic disc as in the case of a conventional fundus camera And a position for acquiring an image centered on the fundus center between the macula and the optic disc. It is also possible to arbitrarily change the display position of the fixation target.

  Further, the fundus camera unit 2 is provided with an alignment optical system 50 and a focus optical system 60 as in a conventional fundus camera. The alignment optical system 50 generates an index (alignment index) for performing alignment (alignment) of the apparatus optical system with respect to the eye E. The focus optical system 60 generates an index (split index) for focusing on the fundus oculi Ef.

  The light (alignment light) output from the LED 51 of the alignment optical system 50 is reflected by the dichroic mirror 55 via the apertures 52 and 53 and the relay lens 54, passes through the hole of the aperture mirror 21, and reaches the dichroic mirror 46. And is projected onto the cornea of the eye E by the objective lens 22.

  The corneal reflection light of the alignment light passes through the objective lens 22, the dichroic mirror 46 and the hole, part of which passes through the dichroic mirror 55, passes through the focusing lens 31, is reflected by the mirror 32, and is half mirror The light passes through 39A, is reflected by the dichroic mirror 33, and is projected onto the light receiving surface of the CCD image sensor 35 by the condenser lens. The light reception image (alignment index) by the CCD image sensor 35 is displayed on the display device 3 together with the observation image. The user can manually perform alignment while visually recognizing the alignment index. Although details will be described later, the arithmetic control unit 2000 can perform alignment by analyzing the position of the alignment index and moving the optical system (auto-alignment function). In this embodiment, since auto-alignment can be performed using an anterior eye camera 3000 described later, it is not essential that auto-alignment using an alignment index is possible. However, the auto-alignment using the alignment index can be performed when the auto-alignment using the anterior segment camera 3000 is not successful, or the auto-alignment using the anterior segment camera 3000 and the alignment index are used. It is also possible to configure so that auto alignment can be used selectively.

  When performing the focus adjustment, the reflecting surface of the reflecting rod 67 is obliquely provided on the optical path of the illumination optical system 10. The light (focus light) output from the LED 61 of the focus optical system 60 passes through the relay lens 62, is separated into two light beams by the split indicator plate 63, passes through the two-hole aperture 64, and is reflected by the mirror 65, The light is focused on the reflecting surface of the reflecting bar 67 by the condenser lens 66 and reflected. Further, the focus light passes through the relay lens 20, is reflected by the perforated mirror 21, passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus oculi Ef.

  The fundus reflection light of the focus light is detected by the CCD image sensor 35 through the same path as the cornea reflection light of the alignment light. A light reception image (split index) by the CCD image sensor 35 is displayed on the display device 3 together with the observation image. The user can manually adjust the focus while visually checking the split index, similarly to the conventional fundus camera. Although details will be described later, the arithmetic control unit 2000 can perform focus adjustment by analyzing the position of the split index and moving the focusing lens 31 and the focus optical system 60 (autofocus function).

  The dichroic mirror 46 branches the optical path for OCT measurement from the optical path for fundus photography. The dichroic mirror 46 reflects light in a wavelength band used for OCT measurement and transmits light for fundus photographing. In this optical path for OCT measurement, a collimator lens unit 40, an optical path length changing unit 41, a galvano scanner 42, a focusing lens 43, a mirror 44, and a relay lens 45 are provided in this order from the OCT unit 1000 side. It has been.

  The optical path length changing unit 41 is movable in the optical axis direction (the direction of the arrow shown in FIG. 12), and changes the optical path length of the optical path for OCT measurement (signal optical path). By changing the optical path length of the signal optical path, the difference (optical path length difference) between the optical path length of the signal optical path and the optical path length of the reference optical path is changed. The change in the optical path length difference is used for correcting the optical path length according to the axial length of the eye E or adjusting the interference state. In this embodiment, the optical path length difference is changed according to the movement (alignment) of the optical system. The optical path length changing unit 41 includes, for example, a corner cube and a drive mechanism that moves the corner cube.

  The configuration of the optical path length difference changing unit is not limited to this. For example, a corner cube similar to the above can be provided in the middle of the reference optical path, and a drive mechanism for moving the corner cube can be provided. Further, the optical path length of the reference optical path can be changed by disposing a reflection mirror (reference mirror) at the end of the reference optical path and moving the reference mirror in the traveling direction of the reference light. Further, the optical path length of the signal optical path can be changed by moving the optical system (measurement optical system) itself that contributes to OCT measurement with respect to the eye to be examined. In general, the optical path length difference changing unit has an arbitrary configuration capable of changing the optical path length of the signal optical path and / or the reference optical path.

  The galvano scanner 42 changes the traveling direction of light (signal light) passing through the optical path for OCT measurement. Thereby, the fundus oculi Ef can be scanned with the signal light. The galvano scanner 42 includes, for example, a galvano mirror that scans signal light in the x direction, a galvano mirror that scans in the y direction, and a mechanism that drives these independently. Thereby, the signal light can be scanned in an arbitrary direction on the xy plane.

  The fundus camera unit 2 is provided with an anterior eye camera 3000. The anterior segment camera 3000 images the anterior segment Ea substantially simultaneously from different directions. In this embodiment, two cameras are provided on the subject-side surface of the fundus camera unit 2 (anterior eye camera). Further, as shown in FIG. 12, the two anterior eye cameras 3000 are respectively provided at positions deviated from the optical path of the illumination optical system 10 and the optical path of the photographing optical system 30. In the following, the two anterior eye cameras may be collectively represented by reference numeral 3000.

  In this embodiment, two anterior eye cameras are provided, but the number of anterior eye cameras in the present invention is an arbitrary number of 2 or more. However, in consideration of the arithmetic processing described later, a configuration that can photograph the anterior segment substantially simultaneously from two different directions is sufficient. In this embodiment, the anterior segment camera 3000 is provided separately from the illumination optical system 10 and the imaging optical system 30, but at least the imaging optical system 30 can be used to perform similar anterior segment imaging. . That is, one of the two or more anterior segment cameras may be carried by a configuration including the imaging optical system 30. Anyway, this embodiment should just be comprised so that imaging | photography of the anterior ocular segment can be carried out substantially simultaneously from two different (or more) directions.

  Note that “substantially simultaneously” indicates that a photographing timing shift that allows negligible eye movement is allowed in photographing with two or more anterior segment cameras. 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.

[OCT unit]
An example of the configuration of the OCT unit 1000 will be described with reference to FIG. The OCT unit 1000 is provided with an optical system for acquiring an OCT image of the fundus oculi Ef. This optical system has the same configuration as a conventional spectral domain type OCT apparatus. That is, this optical system divides low-coherence light into reference light and signal light, and generates interference light by causing interference between the signal light passing through the fundus oculi Ef and the reference light passing through the reference optical path. It is configured to detect spectral components. This detection result (detection signal) is sent to the arithmetic control unit 2000.

  In the case of a swept source type OCT apparatus, a wavelength swept light source is provided instead of a light source that outputs a low coherence light source, and an optical member that spectrally decomposes interference light is not provided. In general, for the configuration of the OCT unit 1000, a known technique according to the type of optical coherence tomography can be arbitrarily applied.

  The light source unit 1001 outputs a broadband low-coherence light L0. The low coherence light L0 includes, for example, a near-infrared wavelength band (about 800 nm to 900 nm) and has a temporal coherence length of about several tens of micrometers. Note that near-infrared light having a wavelength band that cannot be visually recognized by the human eye, for example, a center wavelength of about 1040 to 1060 nm, may be used as the low-coherence light L0.

  The light source unit 1001 includes a light output device such as a super luminescent diode (SLD), an LED, or an SOA (Semiconductor Optical Amplifier).

  The low coherence light L0 output from the light source unit 1001 is guided to the fiber coupler 1003 by the optical fiber 1002, and is divided into the signal light LS and the reference light LR.

  The reference light LR is guided by the optical fiber 1004 and reaches the optical attenuator (attenuator) 1005. The optical attenuator 1005 automatically adjusts the amount of the reference light LR guided to the optical fiber 1004 under the control of the arithmetic control unit 2000 using a known technique. The reference light LR whose light amount is adjusted by the optical attenuator 1005 is guided by the optical fiber 1004 and reaches the polarization adjuster (polarization controller) 1006.

  The polarization adjuster 1006 is a device that adjusts the polarization state of the reference light LR guided through the optical fiber 1004 by applying external stress to the looped optical fiber 1004, for example. Note that the configuration of the polarization adjuster 1006 is not limited to this, and any known technique can be used. The reference light LR whose polarization state is adjusted by the polarization adjuster 1006 reaches the fiber coupler 1009.

  It is also possible to provide a polarization adjuster that adjusts the polarization state of the signal light LS. In general, the polarization state of the signal light LS and / or the reference light LR can be changed. Thereby, the polarization state of the signal light LS and the polarization state of the reference light LR are matched, and the interference efficiency is improved.

  The signal light LS generated by the fiber coupler 1003 is guided by the optical fiber 1007 and converted into a parallel light beam by the collimator lens unit 40. Further, the signal light LS reaches the dichroic mirror 46 via the optical path length changing unit 41, the galvano scanner 42, the focusing lens 43, the mirror 44, and the relay lens 45. The signal light LS is reflected by the dichroic mirror 46, is refracted by the objective lens 22, and is applied to the fundus oculi Ef. The signal light LS is scattered (including reflection) at various depth positions of the fundus oculi Ef. The backscattered light of the signal light LS from the fundus oculi Ef travels in the same direction as the forward path in the reverse direction, is guided to the fiber coupler 1003, and reaches the fiber coupler 1009 via the optical fiber 1008.

  The fiber coupler 1009 causes the backscattered light of the signal light LS to interfere with the reference light LR that has passed through the optical fiber 1004. The interference light LC generated thereby is guided by the optical fiber 1010 and emitted from the emission end 1011. Further, the interference light LC is converted into a parallel light beam by the collimator lens 1012, dispersed (spectral decomposition) by the diffraction grating 1013, condensed by the condenser lens 1014, and projected onto the light receiving surface of the CCD image sensor 1015. Although the diffraction grating 1013 shown in FIG. 13 is a transmission type, other types of spectroscopic elements such as a reflection type diffraction grating may be used.

  The CCD image sensor 1015 is, for example, a line sensor, and detects each spectral component of the split interference light LC and converts it into electric charges. The CCD image sensor 1015 accumulates this electric charge, generates a detection signal, and sends it to the arithmetic control unit 2000.

  In this embodiment, a Michelson type interferometer is employed, but any type of interferometer such as a Mach-Zehnder type can be appropriately employed. Further, in place of the CCD image sensor, another form of image sensor such as a CMOS (Complementary Metal Oxide Semiconductor) image sensor can be used. In addition, when the swept source type OCT is applied, the diffraction grating 1013 is not necessary, and a balanced photodiode or the like is provided in place of the CCCD image sensor 1015.

[Calculation control unit]
The configuration of the arithmetic control unit 2000 will be described. The arithmetic control unit 2000 analyzes the detection signal input from the CCD image sensor 1015 and forms an OCT image of the fundus oculi Ef. The arithmetic processing for this is the same as that of a conventional spectral domain type OCT apparatus.

  The arithmetic control unit 2000 controls each part of the fundus camera unit 2, the display device 3, and the OCT unit 1000. For example, the arithmetic control unit 2000 displays an OCT image of the fundus oculi Ef on the display device 3.

  As the control of the fundus camera unit 2, the arithmetic control unit 2000 controls the operation of the observation light source 11, the imaging light source 15 and the LEDs 51 and 61, the operation control of the LCD 39, the movement control of the focusing lenses 31 and 43, and the reflector 67. Movement control, movement control of the focus optical system 60, movement control of the optical path length changing unit 41, operation control of the galvano scanner 42, operation control of the anterior eye camera 3000, and the like are performed.

  As control of the OCT unit 1000, the arithmetic control unit 2000 performs operation control of the light source unit 1001, operation control of the optical attenuator 1005, operation control of the polarization adjuster 1006, operation control of the CCD image sensor 1015, and the like.

  The arithmetic control unit 2000 includes, for example, a microprocessor, a RAM, a ROM, a hard disk drive, a communication interface, and the like, like a conventional computer. A computer program for controlling the ophthalmologic apparatus 1 is stored in a storage device such as a hard disk drive. The arithmetic control unit 2000 may include various circuit boards, for example, a circuit board for forming an OCT image. The arithmetic control unit 2000 may include an operation device (input device) such as a keyboard and a mouse, and a display device such as an LCD.

  The fundus camera unit 2, the display device 3, the OCT unit 1000, and the calculation control unit 2000 may be configured integrally (that is, in a single casing) or separated into two or more cases. It may be.

[Control system]
The configuration of the control system of the ophthalmologic apparatus 1 will be described with reference to FIG.

(Control part)
The control system of the ophthalmologic apparatus 1 is configured around the control unit 210. The control unit 210 includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, communication interface, and the like. The control unit 210 includes a main control unit 211, a storage unit 212, and an optical system position acquisition unit 213.

(Main control unit)
The main control unit 211 performs the various controls described above. In particular, the main control unit 211 includes an optical path length changing unit 41, a galvano scanner 42, a focusing lens 31, a focusing optical system 60 (imaging focusing driving unit 500), and a focusing lens 43 (OCT focusing driving) of the fundus camera unit 2. Unit 600), the entire optical system (optical system driving unit 700), and the like. Further, the main control unit 211 controls the light source unit 1001, the optical attenuator 1005, the polarization adjuster 1006, and the like of the OCT unit 1000.

  The imaging focus driving unit 500 moves the focusing lens 31 in the optical axis direction of the imaging optical system 30 and moves the focus optical system 60 in the optical axis direction of the illumination optical system 10. Thereby, the focus position of the photographic optical system 30 is changed. The imaging focus driving unit 500 may have a mechanism for moving the focusing lens 31 and a mechanism for moving the focus optical system 60 individually. The photographing focus driving unit 500 is controlled when performing focus adjustment.

  The OCT focusing drive unit 600 moves the focusing lens 43 in the optical axis direction of the signal optical path. Thereby, the focus position of the signal light LS is changed. The focusing position of the signal light LS corresponds to the depth position (z position) of the beam waist of the signal light LS.

  The optical system driving unit 700 moves the optical system provided in the fundus camera unit 2 three-dimensionally. This control is used in alignment and tracking. Tracking is to move the apparatus optical system in accordance with the eye movement of the eye E. When tracking is performed, alignment and focus adjustment are performed in advance. The tracking is a function of maintaining a suitable positional relationship in which the position of the apparatus optical system follows the eye movement to match the alignment, focus, depth position of the beam waist of the signal light LS, and the like.

  Further, since the anterior eye camera 3000 of this embodiment is provided in the housing of the fundus camera unit 2, the anterior eye camera 3000 can be moved by controlling the optical system driving unit 700. Further, it is possible to provide a photographing moving unit that can independently move two or more anterior eye cameras 3000. Specifically, the imaging moving unit may include a drive mechanism (an actuator, a power transmission mechanism, etc.) provided for each anterior segment camera 3000. In addition, the photographing moving unit is configured to move two or more anterior eye cameras 3000 by transmitting power generated by a single actuator by a power transmission mechanism provided for each anterior eye camera 3000. May be.

  The main control unit 211 performs a process of writing data to the storage unit 212 and a process of reading data from the storage unit 212.

(Memory part)
The storage unit 212 stores various data. Examples of the data stored in the storage unit 212 include OCT image image data, fundus image data, and examined eye information. The eye information includes information about the subject such as patient ID and name, and information about the eye such as left / right eye identification information. The storage unit 212 stores various programs and data for operating the ophthalmologic apparatus 1.

  Although illustration is omitted, the storage unit 212 stores in advance information (operation condition information) for executing a plurality of preliminary operations before performing OCT measurement. Preliminary operations include alignment, focus adjustment (focus coarse adjustment), small pupil determination, optical path length difference adjustment, polarization adjustment, focus adjustment (focus fine adjustment), re-alignment (and optical path length difference adjustment), and the like. The plurality of preliminary operations are executed in a predetermined order. In this embodiment, the processes are executed in the above order. However, the type and order of the preliminary operation are not limited to this and are arbitrary.

  Here, the coarse focus adjustment is a focus adjustment using the above-described split index. The focus coarse adjustment is performed by determining the position of the focusing lens 43 based on the information obtained by associating the eye refractive power acquired in advance with the position of the focusing lens 43 and the measured value of the refractive power of the eye to be examined. Can also be performed. On the other hand, the focus fine adjustment is performed based on the interference sensitivity of the OCT measurement. For example, by performing OCT measurement of the eye E to obtain an interference signal and monitoring the interference intensity (interference sensitivity), the position of the focusing lens 43 that maximizes the interference intensity is obtained, and the position is adjusted to that position. By moving the focal lens 43, focus fine adjustment can be executed.

  The operation condition information includes a transition condition for shifting from one preliminary operation to the next preliminary operation. As for the alignment, since the movement amount of the measurement optical system is acquired by analyzing the front image of the eye E (observation image of the anterior eye portion Ea) as described later, the threshold value of this movement amount is used as the transition condition. It is recorded. For coarse focus adjustment, since the amount of movement of the focusing lens 43 is acquired by analyzing the front image of the eye E (observation image of the fundus oculi Ef), the threshold of this amount of movement is recorded as the transition condition. . Regarding the optical path length difference adjustment, the change amount of the optical path length difference between the signal optical path and the reference optical path is acquired by analyzing the detection result of the interference light LC by the measurement optical system. It is recorded. Regarding the polarization adjustment, the change amount of the polarization state of the signal light LS and / or the reference light LR is obtained by analyzing the detection result of the interference light LC by the measurement optical system. It is recorded. The small pupil determination is a process that is executed almost instantaneously, and the threshold determination is not particularly required, so that it is not necessary to provide transition information. However, the small pupil determination includes stepwise operations such as acquisition of a front image (anterior eye image) of the eye E to be examined, determination processing, and control of the diaphragm 19, so that, for example, completion of one of the intermediate operations is completed. It can be a transition condition. For focus fine adjustment, for example, a threshold value of interference intensity can be set as a transition condition.

  Although not shown, aberration information is stored in the storage unit 212 in advance. In the aberration information, information on distortion aberration generated in the photographed image due to the influence of the optical system mounted on each anterior eye camera 3000 is recorded. Here, the optical system mounted on the anterior segment camera 3000 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 3000 into consideration, the following measurement is performed for each anterior segment camera 3000. The operator prepares a predetermined reference point. The reference point is an imaging target used for detecting distortion. The operator performs multiple shootings while changing the relative position between the reference point and the anterior eye camera 3000. Thereby, a plurality of captured images of the reference point captured from different directions are obtained. The operator generates aberration information of the anterior eye camera 3000 by analyzing a plurality of acquired captured images with a computer. The computer that performs the analysis processing may be the data processing unit 230 or any other computer (such as an inspection computer or a maintenance computer before product shipment).

The analysis process for generating aberration information includes, for example, the following steps:
An extraction step of extracting an image region corresponding to the reference point from each captured image;
A distribution state calculation step of calculating a distribution state (coordinates) of an image area corresponding to a reference point in each captured image;
A distortion aberration calculating step of calculating a parameter representing distortion based on the obtained distribution state;
A correction coefficient calculation step of calculating a coefficient for correcting distortion 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 3000 is associated with the correction coefficient corresponding thereto. The aberration information generated in this way is stored in the storage unit 212 by the main control unit 211. Such generation of aberration information and correction of aberration based on the aberration information are called camera calibration.

(Optical system position acquisition unit)
The optical system position acquisition unit 213 acquires the current position of the inspection optical system mounted on the ophthalmologic apparatus 1. The inspection optical system is an optical system used to optically inspect the eye E. The inspection optical system in the ophthalmologic apparatus 1 (a combination machine of a fundus camera and an OCT apparatus) of this embodiment is an optical system for obtaining an image of the eye to be examined. The inspection optical system includes a “measurement optical system” used for OCT measurement.

  The optical system position acquisition unit 213 receives, for example, information indicating the content of movement control of the optical system driving unit 700 by the main control unit 211, and acquires the current position of the inspection optical system moved by the optical system driving unit 700. To do. A specific example of this process will be described. The main control unit 211 controls the optical system driving unit 700 at a predetermined timing (when the apparatus is activated, when patient information is input, etc.) to move the examination optical system to a predetermined initial position. Thereafter, each time the optical system driving unit 700 is controlled, the main control unit 211 records the control contents. Thereby, a history of control contents is obtained. The optical system position acquisition unit 213 acquires the control content up to the present with reference to this history, and obtains the current position of the inspection optical system based on the control content.

  Further, every time the main control unit 211 controls the optical system driving unit 700, the control content is transmitted to the optical system position acquisition unit 213, and every time the optical system position acquisition unit 213 receives the control content, the inspection optical system is transmitted. The current position may be obtained sequentially.

  As another configuration example, a position sensor that detects the position of the inspection optical system may be provided in the optical system position acquisition unit 213.

  When the current position of the inspection optical system is acquired by the optical system position acquisition unit 213 as described above, the main control unit 211 determines the acquired current position and the eye E to be examined obtained by the analysis unit 235 described later. The inspection optical system can be moved to the optical system driving unit 700 based on the three-dimensional position. Specifically, the main control unit 211 recognizes the current position of the inspection optical system based on the acquisition result by the optical system position acquisition unit 213, and recognizes the three-dimensional position of the eye E based on the analysis result by the analysis unit 235. Then, the main control unit 211 changes the position of the inspection optical system from the current position so that the position of the inspection optical system with respect to the three-dimensional position of the eye E has a predetermined positional relationship. This predetermined positional relationship is such that the positions in the x direction and the y direction coincide with each other and the distance in the z direction becomes a predetermined working distance.

(Image forming part)
The image forming unit 220 forms tomographic image data of the fundus oculi Ef based on the detection signal from the CCD image sensor 1015. This process includes processes such as noise removal (noise reduction), filter processing, dispersion compensation, and FFT (Fast Fourier Transform) as in the conventional spectral domain type optical coherence tomography. In the case of another type of OCT apparatus, the image forming unit 220 executes a known process corresponding to the type.

  The image forming unit 220 includes, for example, the circuit board described above. In this specification, “image data” and “image” based thereon may be identified.

(Data processing part)
The data processing unit 230 processes data acquired by imaging of the eye E and OCT measurement. For example, the data processing unit 230 performs various types of image processing and analysis processing on the image formed by the image forming unit 220. For example, the data processing unit 230 executes various correction processes such as image brightness correction. Further, the data processing unit 230 performs various types of image processing and analysis processing on the image (fundus image, anterior eye image, etc.) obtained by the fundus camera unit 2.

  The data processing unit 230 performs known image processing such as interpolation processing for interpolating pixels between tomographic images to form image data of a three-dimensional image of the fundus oculi Ef. Note that the image data of a three-dimensional image means image data in which pixel positions are defined by a three-dimensional coordinate system. As image data of a three-dimensional image, there is image data composed of voxels arranged three-dimensionally. This image data is called volume data or voxel data. When displaying an image based on volume data, the data processing unit 230 performs rendering processing (volume rendering, MIP (Maximum Intensity Projection), etc.) on the volume data, and views the image from a specific gaze direction. Image data of a pseudo three-dimensional image is formed. This pseudo three-dimensional image is displayed on a display device such as the display unit 240A.

  It is also possible to form stack data of a plurality of tomographic images as image data of a three-dimensional image. The stack data is image data obtained by three-dimensionally arranging a plurality of tomographic images obtained along a plurality of scanning lines based on the positional relationship of the scanning lines. That is, stack data is image data obtained by expressing a plurality of tomographic images originally defined by individual two-dimensional coordinate systems by one three-dimensional coordinate system (that is, by embedding them in one three-dimensional space). is there.

  The data processing unit 230 that functions as described above includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, circuit board, and the like. In a storage device such as a hard disk drive, a computer program for causing the microprocessor to execute the above functions is stored in advance.

(User interface)
The user interface 240 includes a display unit 240A and an operation unit 240B. The display unit 240A includes the display device of the arithmetic control unit 2000 and the display device 3 described above. The operation unit 240B includes the operation device of the arithmetic control unit 2000 described above. The operation unit 240B may include various buttons and keys provided on the housing of the ophthalmologic apparatus 1 or outside. For example, when the fundus camera unit 2 has a housing similar to that of a conventional fundus camera, the operation unit 240B may include a joystick, an operation panel, or the like provided on the housing. The display unit 240 </ b> A may include various display devices such as a touch panel provided on the housing of the fundus camera unit 2.

  The display unit 240A and the operation unit 240B do not need to be configured as individual devices. For example, a device in which a display function and an operation function are integrated, such as a touch panel, can be used. In that case, the operation unit 240B includes the touch panel and a computer program. The operation content for the operation unit 240B is input to the control unit 210 as an electrical signal. Further, operations and information input may be performed using a graphical user interface (GUI) displayed on the display unit 240A and the operation unit 240B.

(Modification 1)
In the light shielding plate 100 according to the above-described embodiment, for example, a rubber material is used in order to satisfy the above-described conditions of rigidity, flexibility, and elasticity. However, the entire light shielding plate 100 need not be made of a rubber material or the like. For example, a portion of the light shielding plate 100 that is desired to be deformable (a part on the upper edge side or a side edge side) is made of a rubber material, and other parts can be made of a material having other functions. Examples of the other material include a highly rigid material for maintaining the posture of the light shielding plate 100.

  The illustrated light shielding plate 100 is formed to have a substantially uniform thickness, but is not limited to such a configuration. For example, it is possible to increase the flexibility by thinning at least a part of the upper edge side or both side edges of the peripheral edge of the light shielding plate 100, and to increase the thickness of the other parts to maintain the posture.

(Modification 2)
The light shielding plate 100 according to the embodiment is configured so that the opening operation can be easily performed by the flexibility of the rubber material or the like. However, the light shielding plate 100 can achieve the same effect by other configurations. For example, a configuration in which a slit-like cut is formed from the right edge (and / or the left edge) of the upper edge of the light shielding plate 100 toward the center of the light shielding plate 100 can be applied. This cut is formed so as to penetrate the light shielding plate 100 in the front-rear direction. Further, this notch is closed when no external force is applied, but opens when an external force is applied by an inspector's finger or jig. As a result, access to the eye to be examined becomes possible, and the original shading function is reproduced as the access ends.

(Modification 3)
In the light-shielding plate 100 according to the above-described embodiment, the lower end edge portion is formed in a concave shape recessed upward. This is because the lower edge portion of the light shielding plate 100 is formed in accordance with the outer shape of the ophthalmologic apparatus 1 ophthalmic apparatus 1 (the lens barrel 1a and the casing), thereby more appropriately blocking external light. However, it is also possible to achieve the same effect while making the lower edge portion of the light shielding plate 100 have another configuration. Hereinafter, such a modification will be described with reference to FIG. FIG. 15 is a schematic front view showing the configuration of the light shielding plate 100 according to this modification.

  For example, the lower edge portion of the light shielding plate 100 may be made of a deformable gel material or the like. According to this configuration, by pressing the light shielding plate 100 against the housing of the ophthalmologic apparatus 1, the lower edge portion of the light shielding plate 100 is in close contact with the housing, so that the light shielding function can be ensured.

  In addition to the second recess 105, a plurality of cuts are formed from the lower edge (the portion corresponding to the second recess 105) toward the upper edge as shown in FIG. It is also possible to provide it. Since the lower side of the main body of the light shielding plate 100 is formed in a strip shape, when the light shielding plate 100 is connected to the ophthalmic apparatus 10, the strip portion is retracted to the housing of the ophthalmic apparatus 1, and the light shielding plate 100 The lower edge is adapted to the outer shape of the housing. In this case, the recess may not be provided. Note that the strips are provided sufficiently densely to ensure a light shielding function.

[Second Embodiment]
The light shielding plate 100 and the ophthalmologic apparatus 1 according to the second embodiment will be described with reference to FIGS. Note that description of portions common to the first embodiment is omitted.

  FIG. 16 is a schematic perspective view showing the configuration of the light shielding plate 100 according to the second embodiment. FIG. 17 is a schematic perspective view of the light shielding plate 100 and the ophthalmologic apparatus 1 according to the second embodiment. FIG. 18 is a schematic perspective view showing the light shielding plate 100 according to the second embodiment and an ophthalmic apparatus having a shape different from that in FIG. The ophthalmologic apparatus 1 in FIG. 18 differs from the ophthalmologic apparatus 1 in FIG. 17 in the shape around the lens barrel 1a in the housing. Note that the circle shown in FIG. 16 emphasizes the cut assist lines (105d, 105e) and is not a constituent element of the light shielding plate 100. 17 and 18 show an outline of an example of different types of ophthalmologic apparatuses 1, and the display device 3, the forehead rest 5, the chin rest 7 and the like are not shown.

  As shown in FIG. 16, the light shielding plate 100 according to the second embodiment is cut to cut out a part of the light shielding plate 100 at each of the first side portion 105 b and the second side portion 105 c in the lower second concave portion 105. Auxiliary lines (105d, 105e) are provided.

  As shown in a circled portion in FIG. 16, the first side portion 105b is provided with a cutting assist line 105d. The cut assisting line 105d is a guide for cutting a part of the lower edge of the light shielding plate 100. Similarly, a cut auxiliary line 105e is provided on the second side portion 105c as a guide for cutting a part of the lower edge portion of the light shielding plate 100. The cut auxiliary line 105d and the cut auxiliary line 105e in this example have a symmetrical shape.

  The cut assist lines 105d and 105e are for making the shape of the lower edge of the periphery of the light shielding plate 100 correspond to the shape of the housing of the ophthalmologic apparatus. For example, in the case of the shape of the housing of the ophthalmic apparatus 1 as shown in FIG.

  On the other hand, in the case of the shape of the housing of the ophthalmologic apparatus 1 as shown in FIG. 18, the shape of the lower edge of the light shielding plate 100 is not compatible with this, and therefore the lower edge portion along the cutting assist lines 105 d and 105 e. By cutting out a part, it is possible to adapt the shape of the lower edge to the shape of the housing of the ophthalmologic apparatus 1 (around the lens barrel 1a).

  The cut assist lines 105d and 105e are configured as perforations in one example. That is, through holes are provided at predetermined intervals along the cut auxiliary lines 105d and 105e.

  As another example, portions corresponding to the cut assist lines 105d and 105e can be formed thinner than other portions. Further, the brittleness of the portion can be increased by a method other than thinning.

  Moreover, you may attach | subject the mark which shows the cutting assistance lines 105d and 105e. In this case, a part of the lower edge portion of the light shielding plate 100 can be cut out along the mark with a scissors or the like. According to some configurations exemplified here, the light-shielding plate 100 can be arranged so that no gap is generated between the ophthalmologic apparatus 1 and external light can be suitably blocked.

  It should be noted that the several embodiments and some modifications described above can be combined as appropriate.

(Action / Effect)
The operation and effect of the light shielding plate 100 and the ophthalmologic apparatus 1 according to the embodiment described above will be described.

  Since the light shielding plate 100 described above has a lower end edge formed in accordance with the outer shape of the ophthalmic apparatus 1, it is in contact with the ophthalmic apparatus 1 without a gap when connected to the ophthalmic apparatus 1. Further, the light shielding plate 100 is slightly longer in length in the left-right direction (width) than the forehead pad 5. The shape of the light shielding plate 100 is curved so as to be concave toward the subject. According to such a configuration, it is possible to prevent external light entering the eye of the subject or external light from entering the optical system of the ophthalmologic apparatus 1 such as an objective lens, and compared with a conventional dark curtain. Thus, it can be easily attached to the ophthalmic apparatus 1. Therefore, the work efficiency concerning inspection improves.

  Further, the light shielding plate 100 has such a rigidity that it can maintain its posture or shape while being supported by the connection member 200. Further, the light shielding plate 100 has flexibility that can be deformed by receiving an external force. Therefore, a person who examines the subject with the ophthalmologic apparatus 1 can access the subject's eye and its surroundings by bending and bending the light shielding plate 100.

  That is, according to the light-shielding plate 100 of the present embodiment, the function of blocking the external light by connecting to the ophthalmologic apparatus 1 is sufficiently exhibited, and from this state, it is easy to open the subject facing the ophthalmologic apparatus 1. It is possible to migrate to. Furthermore, since the light shielding plate 100 has elasticity, the application of force to the light shielding plate 100 is canceled when access to the eye to be examined is completed, and the light shielding plate 100 returns to its original shape from the deformed state.

  Further, the light shielding plate 100 is curved toward the subject side, and the surface on the subject side is black. That is, reflection of external light on the front surface of the light shielding plate 100 is suppressed, and reflection of external light to the subject side through the light shielding plate 100 is reduced. That is, the light-shielding plate 100 can reduce the possibility of obstructing photographing and measurement by the ophthalmologic apparatus by providing a configuration that avoids miosis and external light intrusion into the optical system of the ophthalmologic apparatus 1.

  The light shielding plate 100 according to the second embodiment includes a cutting auxiliary line (105d) that allows a part of the light shielding plate 100 to be cut off at each of the first side portion 105b and the second side portion 105c in the lower second concave portion 105. , 105e). The cut auxiliary lines 105d and 105e are for facilitating cutting of a part of the lower edge portion of the light shielding plate 100. The person who performs the examination can adapt the shape of the lower edge of the light shielding plate 100 to the shape of the housing by cutting out a part along the auxiliary line according to the shape of the housing of the ophthalmologic apparatus 1. It is.

  Therefore, since the light shielding plate 100 can be applied to a plurality of ophthalmologic apparatuses 1, the versatility of the light shielding plate 100 can be improved.

  The configuration described above is merely an example for favorably implementing the present invention. Therefore, arbitrary modifications (omitted, replacement, addition, etc.) within the scope of the present invention can be made as appropriate.

DESCRIPTION OF SYMBOLS 1 Ophthalmic apparatus 1a Lens tube 100 Light-shielding plate 101a, 101b Connection part 103 1st recessed part 105 2nd recessed part 105a Middle part 105b 1st side part 105c 2nd side part 105d, 105e Cut-off auxiliary line 200 Connection member 201 Main body part 201a, 201b Holding part 203a, 203b Engagement part

Claims (13)

A light-shielding plate for preventing external light from entering the eye of the subject and the optical system of the ophthalmic apparatus,
A mounting portion for mounting on the ophthalmic apparatus;
In a state of being mounted on the ophthalmologic apparatus via the mounting unit, the face of the subject is disposed opposite to at least a portion around the subject eye, and at least when accessing the subject's eye or its surroundings. A light shielding plate comprising: a plate-shaped light shielding portion whose upper edge portion and / or side edge portion can be deformed by receiving an external force. The light shielding plate according to claim 1, wherein an upper end edge of the light shielding portion is formed in a concave shape. The light shielding plate according to claim 1, wherein a lower end edge of the light shielding part is formed in a concave shape. The light-shielding plate according to any one of claims 1 to 3, wherein the deformable portion of the light-shielding portion is formed of a flexible material. The light shielding plate according to claim 4, wherein the material is an elastic material. The light shielding plate according to any one of claims 1 to 5, wherein a guide line for cutting a predetermined portion including a part of a lower end edge of the light shielding portion is provided. The light shielding plate according to claim 6, wherein in the light shielding portion, the guide line is formed thinner than other portions. It can be attached to the first ophthalmic device and the second ophthalmic device having different appearance shapes,
The lower edge has a shape that follows the external shape of the first ophthalmic apparatus,
The light-shielding plate according to claim 6 or 7, wherein the lower end edge after the predetermined portion is cut has a shape that conforms to the external shape of the second ophthalmic apparatus. The light shielding plate according to any one of claims 1 to 8, wherein a surface of the light shielding portion that faces the subject's face is formed in a concave shape. The light-shielding plate according to claim 1, wherein a surface of the light-shielding portion that faces the subject's face is black. 11. The light shielding plate according to claim 1, wherein the region on the lower edge portion side of the light shielding portion is formed in a strip shape including a plurality of cuts. An ophthalmologic apparatus having an optical system and a light-shielding plate for preventing incidence of external light on the subject's eye and the optical system,
The shading plate is
A mounting portion for mounting on the ophthalmic apparatus;
In a state of being mounted on the ophthalmologic apparatus via the mounting unit, the face of the subject is disposed opposite to at least a portion around the subject eye, and at least when accessing the subject's eye or its surroundings. An ophthalmologic apparatus comprising: a plate-shaped light-shielding portion whose upper edge portion and / or side edge portion can be deformed by receiving an external force. A movable arm having a proximal end attached to the ophthalmic apparatus main body, and a fixation lamp provided at a distal end portion of the movable arm, for fixing the eye to be examined in a direction outside the optical path of the optical system. Further having an external fixation target,
The ophthalmologic apparatus according to claim 12, wherein an upper end edge of the light shielding plate is formed in a concave shape so as not to interfere with at least a part of a movable range of the movable arm.