JP7117120B2 - ophthalmic equipment - Google Patents

Description

The present invention relates to an ophthalmic device.

Conventionally, an ophthalmologic apparatus includes an illumination system that irradiates an eye to be inspected with illumination light and an observation system for observing the eye to be inspected, and adjusts the light intensity of the light source of the illumination system by detecting the amount of light reflected from the eye to be inspected. is known (see, for example, Patent Document 1).

JP-A-2002-224036

By the way, the conventional ophthalmologic apparatus detects the amount of reflected light from the subject's eye, but this reflected light amount varies depending on the condition of the subject's eye, the accuracy of the sensor, variations, and the like. In particular, the amount of reflected light varies greatly when the object to be observed such as the cross section of the eye, the anterior segment of the eye, or the fundus of the eye is different. Therefore, it has been difficult to accurately grasp the actual illumination state of the eye to be inspected and appropriately control the amount of illumination light by detecting the amount of light reflected from the eye to be inspected.

SUMMARY OF THE INVENTION It is an object of the present invention to provide an ophthalmologic apparatus capable of accurately grasping the actual illumination condition of an eye to be inspected and appropriately controlling the amount of illumination light.

In order to achieve the above object, an ophthalmologic apparatus of the present invention provides a light shielding member that irradiates an eye to be inspected with illumination light and that is arranged at a position optically conjugate with the eye to be inspected to partially block the luminous flux of the illumination light. an observation system for observing or photographing the light reflected by the eye to be examined; and an observation system provided on the light shielding member and provided at a position for detecting the amount of illumination light at a position optically conjugate with the eye to be examined. and a light intensity detector.

In the ophthalmologic apparatus configured as described above, the light amount detector can detect the amount of illumination light at a position optically conjugate with the eye to be examined, and the amount of illumination light obtained by the illumination state at the position of the eye to be examined can be detected. can detect a light amount approximately equal to that of the Therefore, it is possible to accurately grasp the actual illumination state of the subject's eye.

1 is a side view showing the overall configuration of an ophthalmologic apparatus of Example 1. FIG. FIG. 2 is an explanatory diagram showing the optical system of the ophthalmologic apparatus of Example 1; 2 is a plan view showing a field stop portion of the ophthalmologic apparatus of Example 1. FIG. 4 is a flowchart showing illumination light control processing executed by an illumination light control unit of the ophthalmologic apparatus of Example 1. FIG. FIG. 11 is an explanatory diagram showing a field stop portion of the ophthalmologic apparatus of Example 2; FIG. 11 is a plan view showing the field stop portion of the ophthalmologic apparatus of Example 2; FIG. 11 is an explanatory diagram showing the optical system of the ophthalmologic apparatus of Example 3; FIG. 11 is an explanatory diagram showing a slit portion of a modified example of the ophthalmologic apparatus of Example 2;

Hereinafter, a mode for carrying out the ophthalmologic apparatus of the present invention will be described based on Examples 1 to 3 shown in the drawings.

(Example 1)
The configuration of the ophthalmologic apparatus 10 of the first embodiment will be described by dividing it into "overall configuration", "detailed configuration of illumination system", "detailed configuration of observation system", and "detailed configuration of illumination light control processing".

[overall structure]
The ophthalmologic apparatus 10 shown in FIG. 1 is a slit lamp microscope that obtains a cross-sectional image of the cornea by cutting a light section of the cornea of an eye E to be examined using slit light.

The ophthalmologic apparatus 10 of Example 1 includes a microscope body 11, an illumination system 12, an observation system 13, and an illumination light controller 20, as shown in FIG. The ophthalmologic apparatus 10 has a background illumination system (not shown). The background illumination system illuminates the area around the illumination area of the slit light emitted from the illumination system 12 with background light.

A microscope body 11 is installed on the table 1 and supports an illumination system 12, an observation system 13, and a background illumination unit 20, respectively. The microscope main body 11 is supported by a pedestal 11a fixed to the upper surface of the table 1, a base 14 provided on the upper surface of the pedestal 11a, a support portion 15 provided on the upper surface of the base 14, and the pedestal 11a. a chin rest 16;

The base 14 is installed so as to be movable in the front-rear direction and the left-right direction when viewed from the subject's eye E via a movement mechanism 14a with respect to the pedestal 11a. The base 14 is moved by tilting the operation handle 14b. Further, by rotating the operation handle 14b about its axis, the support portion 15 provided on the upper surface of the base 14 moves vertically.

The support portion 15 has a pedestal 15a, a first support arm 15b, and a second support arm 15c.
A pedestal 15a is provided on the upper surface of the base 14, and a first support arm 15b and a second support arm 15c are erected from the pedestal 15a. Here, the first support arm 15b and the second support arm 15c are independently rotatable around a coaxial vertical axis.

The first support arm 15 b has an illumination system housing 12 a that accommodates the illumination system 12 attached to the upper part thereof, and supports the illumination system 12 . This first support arm 15b is manually rotated. The illumination system housing 12a turns around the subject's eye E by rotating the first support arm 15b. Thereby, the irradiation direction of the slit light with respect to the eye E to be examined is changed. The first support arm 15b may also rotate in the vertical direction, and in this case, the elevation angle and depression angle of the slit light with respect to the eye E to be examined are changed.

The observation system housing 13a containing the observation system 13 is attached to the upper part of the second support arm 15c to support the observation system 13 . This second support arm 15c is manually rotated. As the second support arm 15c rotates, the observation system housing 13a rotates around the first support arm 15b. Thereby, the observation direction of the observation system 13 with respect to the eye E to be examined is changed.

The first support arm 15b and the second support arm 15c may be configured to rotate automatically by electric power. In this case, an actuator for generating driving force for rotating the first and second support arms 15b and 15c and a transmission mechanism for transmitting this driving force are required. A stepping motor (pulse motor), for example, is used as the actuator. Also, the transmission mechanism uses, for example, a combination of gears, a rack and pinion, or the like.

The chin rest 16 is arranged at a position facing the front of the observation system housing 13a. The chin rest 16 is provided with a chin rest 16a and a forehead 16b for stabilizing the subject's face. With this ophthalmologic apparatus 10, the examiner observes the subject's eye E while the examinee faces the table 1 and touches the chin rest 16a and the forehead 16b.

The illumination system 12 irradiates the eye E to be examined with slit light. The illumination system 12 is housed in an illumination system housing 12a. The intensity of the slit light is changed by operating the illumination intensity operation section 14c provided on the base 14. FIG. The “slit light” is light in which a part of the irradiation region is blocked to form a belt-shaped irradiation region, and is illumination light for observing the cornea and fundus of the eye E to be examined.

Further, below the illumination system housing 12a, a mirror 12b that reflects the slit light emitted from the illumination system 12 toward the subject's eye E is arranged. The mirror 12b is attached to the first support arm 15b. In addition, it is also possible to reflect the background light toward the eye E to be examined by this mirror 12b.

The observation system 13 observes and photographs reflected light from the eye E to be examined. Here, the "reflected light" includes not only slit light and background light reflected by the eye E to be examined, but also various kinds of light such as scattered light from the eye E to be examined and its surroundings. In Example 1, these various types of light are collectively referred to as "reflected light". The observation system 13 is housed in an observation system housing 13a. An eyepiece 13b is provided at the end of the observation system housing 13a. The examiner observes the subject's eye E with the naked eye by looking into the eyepiece 13b. An observation magnification operation knob 13c for changing the observation magnification is arranged on the side surface of the observation system housing 13a.

Further, an imaging device 13d for imaging the eye E to be examined is detachably connected to the observation system housing 13a. The imaging device 13d has an imaging device 13e. The imaging element 13e is a photoelectric conversion element that detects light and outputs an electric signal (image signal). The image signal is appropriately input to an external control device (not shown) such as a personal computer connected to the ophthalmologic apparatus 10 . As the imaging element 13e, for example, a CCD (Charge Coupled Device) image sensor or a CMOS (Complementary Metal Oxide Semiconductor) image sensor is used.

The illumination light controller 20 controls the luminous intensity of the main light source 121 of the illumination system 12 . The illumination light control unit 20 includes a control circuit 21 having a CPU (Central Processing Unit), and a storage unit 22 including a ROM (Read Only Memory), a RAM (Random Access Memory), a hard disk drive, and the like.

The control circuit 21 acquires necessary information and outputs appropriate control commands to the illumination system 12 of the ophthalmologic apparatus 10 . On the other hand, the storage unit 22 stores control programs in advance. A control command from the illumination light control unit 20 is realized by the cooperation of this control program and hardware. Note that the illumination light control unit 20 is built in the base 14 .

[Detailed configuration of illumination system]
The illumination system 12 has a main light source 121, a relay lens 122, an illumination diaphragm 123, a condenser lens 124, a light flux controller 128, and an imaging lens 127, as shown in FIG. Reference O1 denotes the optical axis of the illumination system 12 (illumination optical axis).

The main light source 121 is a slit light source for observing the cornea and fundus of the eye E to be examined. The main light source 121 has at least a visible light source that outputs visible light. lamps, LEDs, etc.) may be used. Also, the illumination system 12 may be provided with a plurality of light sources, or may be separately provided with a plurality of monochromatic light sources. The intensity of the main light source 121 is changed by controlling the magnitude of applied electric power based on the control command from the illumination light control section 20 .

The illumination diaphragm 123 has a translucent portion whose size can be changed, and adjusts the illuminance of the illuminated portion.

The luminous flux controller 128 controls the area of the opening 128a through which the illumination luminous flux S (see FIG. 3) of the illumination light emitted from the main light source 121 passes. A slit light is formed in which the irradiation area is restricted in a belt shape. Here, the light flux control unit 128 detects the light shielding member 129 arranged at a position optically conjugate with the eye E to be examined and the light amount (brightness) of the illumination light at a position optically conjugate with the eye E to be examined. and a light intensity detector 130 for detecting the light intensity.

The light shielding member 129 is composed of a slit portion 125 and a field stop portion 126 . In addition, “a position optically conjugate with the eye E to be examined” means a position in a conjugate relationship with the eye E to be examined. Note that the “position optically conjugated with the eye E to be examined” does not have to be a position that is completely conjugated with the eye E to be examined. is negligible)).

The slit section 125 has a pair of slit blades 125a and 125b arranged facing each other across the illumination optical axis O1. The pair of slit blades 125a and 125b move toward or away from each other across the illumination optical axis O1. By changing the interval (slit interval) between the pair of slit blades 125a and 125b, the area that blocks the illumination light beam S (see FIG. 3) is changed, and the width of the slit light is changed. The interval between the pair of slit blades 125a and 125b may be arbitrarily adjustable by manual operation, or may be electrically changeable.

The field stop portion 126 is a disk-shaped turret arranged between the slit portion 125 and the imaging lens 127 and close to the slit portion 125 . As shown in FIG. 3, the field stop portion 126 has a light shielding surface 126a orthogonal to the illumination optical axis O1, and rotates about a rotation center 126α in a direction orthogonal to the illumination optical axis O1. A plurality of apertures 126b to 126f penetrating through the light shielding surface 126a are formed in the field stop portion 126, and the illumination light flux S is partially shielded by the plurality of apertures. Note that the plurality of openings 126b to 126f are different in size and shape from each other.

The light intensity detector 130 is a measuring device (photodetector) that converts light into electricity. It is composed of an electromotive force type photodiode or the like. The light amount detector 130 is provided on the light shielding surface 126a of the field stop portion 126 of the light shielding member 129 arranged at a position optically conjugate with the eye E to be examined.

Also, as shown in FIG. 3, the light quantity detector 130 of Example 1 is arranged on a virtual circle 126β set on the light shielding surface 126a and positioned between the opening 126e and the opening 126f. As a result, the light amount detector 130 can align the light receiving portion 130a with the illumination optical axis O1 by rotating the field stop portion 126 about the center of rotation 126α. When the light receiving portion 130a is aligned with the illumination optical axis O1, the light intensity detector 130 directly receives the illumination light from the main light source 121 on the illumination optical axis O1 and detects the light intensity. The light amount information of the illumination light detected by the light amount detector 130 is input to the illumination light control section 20 .

[Detailed configuration of observation system]
The observation system 13 has a pair of left and right optical systems. The left and right optical systems have almost the same configuration. The examiner can observe the subject's eye E with binoculars through the left and right optical systems. Each optical system of the observation system 13, as shown in FIG. 137 and . Note that only one of the left and right optical systems of the observation system 13 is shown in FIG. Also, the beam splitter 134 is provided in one or both of the left and right optical systems. Furthermore, reference O2 indicates the optical axis of the observation system 13 (observation optical axis).

The eyepiece lens 137 is provided in the eyepiece section 13b. A symbol P indicates a position where the image of the observation site is formed by the imaging lens 135 . The examiner observes this image through the eyepiece 137 . The symbol Ec indicates the cornea of the eye E to be examined, the symbol Ep the iris, and the symbol Er the fundus. Symbol Eo indicates the examiner's eye.

The variable magnification optical system 132 changes the magnification (angle of view) of an image observed by an eyepiece lens 137 of the subject's eye E and a photographed image. The variable-magnification optical system 132 is composed of a plurality of variable-magnification lens groups that can be selectively inserted with respect to the observation optical axis O2. Each variable power lens group has a plurality of (two in FIG. 2) variable power lenses 132a and 132b, which provide different magnifications. Among the variable power lens groups, the variable power lens group arranged on the observation optical axis O2 is used as the variable power optical system 132 . The change in magnification, that is, the switching of the variable magnification lens group arranged on the observation optical axis O2 is performed by operating the observation magnification operation knob 13c. Alternatively, a switch (not shown) or the like may be used to electrically change the magnification (switching of the variable magnification lens group).

The beam splitter 134 splits the light traveling along the observation optical axis O2 into two. The light transmitted through the beam splitter 134 is guided to the examiner's eye Eo via the imaging lens 135, the prism unit 136 and the eyepiece 137. The prism unit 136 has two optical elements 136a and 136b, inverts the image, and changes the width of the left and right observation optical axes O2 according to the interpupillary distance of the examiner.

Also, the light reflected by the beam splitter 134 is guided to the imaging element 13e of the imaging device 13d via the imaging lens 138 and the mirror 139. FIG. The imaging element 13e detects this reflected light and generates an image signal.

[Detailed Configuration of Illumination Light Control Processing]
FIG. 4 is a flow chart showing the flow of illumination light control processing executed by the ophthalmologic apparatus 10 of the first embodiment. Each step in FIG. 4 will be described below.

In step S1, the illumination light controller 20 determines whether or not the main light source 121 of the illumination system 12 is turned on. If YES (the main light source is turned on), the process proceeds to step S2. If NO (the main light source is turned off), step S1 is repeated.

In step S2, following the judgment that the main light source is turned on in step S1, the light amount detector 130 detects the light amount of illumination light at a position optically conjugate with the subject's eye E, and the process proceeds to step S3.
Here, the detection of the amount of light is performed in a state in which the field stop section 126 is rotated and the light receiving section 130a of the light amount detector 130 is aligned with the illumination optical axis O1. Thereby, the light amount detector 130 directly detects the light amount on the illumination optical axis O1. Also, the light amount information of the illumination light detected by the light amount detector 130 is input to the illumination light control section 20 .

In step S3, following the detection of the light amount in step S2, the illumination light control unit 20 estimates the illumination light amount (actual light amount) at the position of the subject's eye E based on the light amount information input from the light amount detector 130. and proceed to step S4.

In step S4, following the estimation of the actual amount of light in step S3, the difference between the actual amount of light estimated in step S3 and a preset target amount of light is obtained. Output a control command for controlling the luminous intensity of the light source 121, and proceed to RETURN.
Here, the luminous intensity of the main light source 121 is controlled by controlling the magnitude of electric power applied to the main light source 121 by the illumination light controller 20 .

The operation of the ophthalmologic apparatus 10 according to the first embodiment will be described separately for "illumination light amount detection operation" and "illumination light amount monitoring operation".

[Light quantity detection action of illumination light]
In the ophthalmologic apparatus 10 of Example 1, the light amount detector 130 is provided on the light shielding surface 126a of the field stop portion 126 of the illumination system 12. FIG. Here, the field stop unit 126 is arranged at a position optically conjugate with the eye E to be examined. Therefore, by providing the light amount detector 130 in the field stop portion 126, the light amount detector 130 is provided at a position for detecting the light amount (brightness) of the illumination light at a position optically conjugate with the eye E to be examined. will be

On the other hand, the illumination state at the position optically conjugate with the eye E to be examined is substantially the same as the illumination state at the position of the eye E to be examined. Also, the illumination state at a position that is not optically conjugate with the eye E to be inspected is different from the illumination state at the position of the eye E to be inspected.
Here, the "illumination state" includes the illuminance, light amount, light beam direction, light beam convergence, etc. at the position (for example, a position optically conjugate with the eye to be examined E, the position of the eye to be examined E, etc.).

In the ophthalmologic apparatus 10 according to the first embodiment, the light amount detector 130 is provided at a position optically conjugate with the eye E to be examined, so that the light amount detector 130 detects the amount of light at a position optically conjugate with the eye E. can detect the amount of illumination light in the Therefore, it is possible to detect the amount of light equivalent to the amount of illumination light at the position of the eye E to be examined, and to accurately grasp the actual illumination state of the eye E to be examined based on the detected amount of light.

The light amount detector 130 of the first embodiment can be executed when the field stop section 126 is rotated and the light receiving section 130a of the light amount detector 130 is aligned with the illumination optical axis O1. Therefore, the light quantity detector 130 does not always detect the light quantity of the illumination light. The amount of light is detected as necessary, such as when checking the amount of illumination light at position E. Therefore, no light amount loss occurs during eye examination, and the observation of the eye to be examined E can be prevented from being affected.

Moreover, the light amount detector 130 of the first embodiment is arranged on the virtual circle 126β set on the light shielding surface 126a. Therefore, when the field stop portion 126 rotates about the rotation center 126α, the light receiving portion 130a is aligned with the illumination optical axis O1. That is, the position where the light amount detector 130 is provided is on the illumination optical axis O1, and is the position where the light amount of the illumination light on the illumination optical axis O1 is detected. Thereby, the light amount detector 130 can detect the light amount of the illumination light on the illumination optical axis O1.

Here, when the light amount is measured at a position off the illumination optical axis O1, the orientation distribution of the main light source 121 affects the detected light amount, and the detected light amount varies depending on the installation position of the light amount detector 130. In particular, when the main light source 121 is an LED, the amount of light varies greatly depending on the orientation angle. In addition, the orientation distribution of the main light source 121 has individual differences and variations. Therefore, it is difficult to accurately detect the amount of illumination light equivalent to the amount of illumination light at the position of the subject's eye E at a position away from the illumination optical axis O1.

On the other hand, in Example 1, the light quantity detector 130 can detect the light quantity of the illumination light on the illumination optical axis O1. The amount of light equivalent to the amount of illumination light can be appropriately detected. As a result, the illumination state of the subject's eye E can be grasped more accurately.

[Light intensity monitoring action of illumination light]
The ophthalmologic apparatus 10 according to the first embodiment executes illumination light control processing. That is, the illumination light control section 20 performs the processing of step S1 shown in the flowchart of FIG. When the illumination light control unit 20 determines that the main light source 121 is turned on, the process of step S2 shown in the flowchart of FIG. 4 is performed. That is, the light amount detector 130 detects the amount of illumination light at a position optically conjugate with the subject's eye E, and inputs information on the amount of illumination light to the illumination light control section 20 .

Then, the processing of steps S3 and S4 shown in the flowchart of FIG. 4 is performed in order. That is, the illumination light control unit 20 estimates the illumination light amount (actual light amount) at the position of the subject's eye E based on the light amount information input from the light amount detector 130 . The illumination light control unit 20 outputs a control command for controlling the magnitude of power applied to the main light source 121 so that the difference between the estimated actual light intensity and the preset target light intensity is equal to or less than a predetermined threshold. do.

As a result, the magnitude of the power applied to the main light source 121 is adjusted, and the amount of illumination light can be appropriately controlled regardless of variations in the main light source 121 and the illumination system 12 . Even if the main light source 121 deteriorates and the illumination light intensity at the position of the eye E to be inspected decreases, the applied power is appropriately adjusted to increase the luminous intensity of the main light source 121 and can recover the amount of illumination light. Furthermore, by exchanging the main light source 121, even when the illumination light intensity at the position of the eye to be examined E changes, the luminous intensity of the main light source 121 can be controlled to obtain an appropriate illumination light intensity. .

(Example 2)
The ophthalmologic apparatus of Example 2 is an example in which a mirror for reflecting illumination light is provided in a light shielding member of an illumination system, and a light quantity detector is provided on the reflected light path of the mirror. The ophthalmologic apparatus of Example 2 will be described below. It should be noted that the same reference numerals as in the first embodiment are assigned to the same configurations as those of the ophthalmologic apparatus 10 of the first embodiment, and detailed description thereof will be omitted.

In the polishing apparatus of Example 2, a mirror 126g is provided on the light shielding surface 126a of the field diaphragm 126 in the light shielding member 129 of the light flux controller 128 of the illumination system 12, as shown in FIG. 5A.

The mirror 126g is a mirror that reflects (total reflection) all incident light. The mirror 126g, as shown in FIG. 5B, is arranged on a virtual circle 126β set on the light shielding surface 126a and positioned between the opening 126e and the opening 126f. As a result, the field stop portion 126 rotates about the rotation center 126α, so that the mirror 126g is aligned with the illumination optical axis O1 and can reflect the light on the illumination optical axis O1. The reflecting surface of the mirror 126g is inclined so as to gradually protrude from the light shielding surface 126a toward the center of rotation 126α. Therefore, the mirror 126g coincides with the illumination optical axis O1, and the reflected optical axis O3 when the light on the illumination optical axis O1 is reflected deviates from the illumination optical axis O1 and goes outside the field stop portion 126.

On the other hand, the light quantity detector 130A of Example 2 is provided on the reflected optical axis O3 of the mirror 126g, as shown in FIG. 5A. As a result, the light amount detector 130A receives the illumination light from the main light source 121 on the side of the field diaphragm 126 via the mirror 126g. Then, the amount of light on the reflected optical axis O3 is detected.

Here, the mirror 126g totally reflects the light on the illumination optical axis O1. Therefore, the light amount detector 130A can detect the same light amount as when the illumination light from the main light source 121 is directly received on the illumination optical axis O1 even at a position off the illumination optical axis O1.

That is, in the ophthalmologic apparatus of the second embodiment, even if the field stop portion 126 of the light shielding member 129 arranged at a position optically conjugate with the eye E to be examined does not have the direct light amount detector 130A, It is possible to detect the amount of illumination light at a position that is physically conjugate. As a result, the light intensity detector 130A can detect a light intensity equivalent to the illumination light intensity at the position of the eye to be inspected E, and the accuracy of grasping the actual illumination state of the eye to be inspected E can be ensured. Layout freedom can be improved.

(Example 3)
The ophthalmologic apparatus 10B of the third embodiment has a laser treatment system that irradiates the subject's eye with treatment light, a light separation member that separates the multiplexed treatment light and the illumination light into a plurality of lights, and a light amount detector. This is an example provided on the separation optical path of the light separation member. The ophthalmologic apparatus 10B of Example 3 will be described below. It should be noted that the same components as those of the first embodiment are given the same reference numerals as those of the first embodiment, and detailed description thereof will be omitted.

The ophthalmologic apparatus 10B of the third embodiment includes an illumination system 12 for irradiating the eye E to be examined with slit light, an observation system 13 for observing and photographing the light reflected by the eye E to be examined, and a therapeutic laser beam for the eye E to be examined. A laser treatment system 30 for irradiating (therapeutic light) is provided. In this ophthalmologic apparatus 10B, a multiplexing mirror 31 (light separating member) is installed on the illumination optical axis O1 of the illumination system 12. As shown in FIG.

Here, the combining mirror 31 is arranged at a position optically conjugated to the eye E to be inspected and at a combining position where the therapeutic laser light and the illumination light are combined. Therefore, the optical axis of the therapeutic laser beam emitted from the laser treatment system 30 (hereinafter referred to as “treatment optical axis O4”) is multiplexed coaxially with the illumination optical axis O1 by the multiplexing mirror 31 . Further, the combining mirror 31 is formed by a dichroic mirror, and reflects the combined wave of the therapeutic laser light and the illumination light toward the eye E to be inspected and the first combined wave in a direction different from the eye E to be inspected. It separates into two lights (optical axis) of the reflected second multiplex. The second multiplexing is a light amount of several percent of the multiplexing of the therapeutic laser light and the illumination light. Further, in FIG. 6, reference O51 indicates the first combined optical axis, and O51 indicates the second combined optical axis (separation optical axis).

On the other hand, the light quantity detector 130B of Example 3 is provided on the split optical path (separation optical axis O52) of the second combining beam split by the combining mirror 31, as shown in FIG. As a result, the light amount detector 130B receives part of the multiplexed beam of the therapeutic laser light and the illumination light at the side of the multiplexing mirror 31, and detects the light amount on the separation optical axis O52.

Here, the multiplexing mirror 31 separates several percent of the multiplexing of the treatment laser light and the illumination light at a position optically conjugated to the eye E to be examined. Therefore, the light amount detector 130B can detect the multiplexing of the therapeutic laser light and the illumination light at a position optically conjugate with the eye E to be examined. Further, the amount of combined light detected by the light amount detector 130B is determined by the separation ratio of the combined light by the combining mirror 31 set in advance. As a result, the light quantity detector 130B can detect a light quantity of a predetermined ratio with respect to the illumination light quantity at the position of the eye to be examined E, and the actual lighting condition of the eye to be examined E can be accurately grasped. .

Furthermore, since the combining mirror 31 always separates the combination of the therapeutic laser light and the illumination light, the light amount detector 130B can always monitor the combined light amount. This makes it possible to quickly detect deterioration of the main light source 121 or the like.

The ophthalmologic apparatus of the present invention has been described above based on Examples 1 to 3, but the specific configuration is not limited to these Examples, and each claim of the scope of claims. Design changes, additions, etc. are permitted as long as they do not deviate from the gist of the invention.

In the second embodiment, an example in which the mirror 126g that totally reflects the light on the illumination optical axis O1 is provided in the field stop portion 126 of the light shielding member 129 is shown. However, it is not limited to this. Since the mirror 126g only needs to reflect the illumination light at a position optically conjugate with the eye E to be examined, for example, as shown in FIG. A mirror 126g may be provided in the slit portion 125 of .

That is, a mirror 126g is provided on the surface 125c of the pair of slit blades 125a and 125b of the slit portion 125 on the side of the main light source 121, and this surface 125c is inclined so as to gradually protrude from the illumination optical axis O1 side toward the periphery. Further, a light amount detector 130A is arranged on the reflected light path (reflected optical axis O3) generated when the pair of slit blades 125a and 125b are closed.
Thus, when the pair of slit blades 125a and 125b are closed, the light intensity detector 130A can detect the light intensity on the illumination optical axis O1 at a position optically conjugate with the eye E to be inspected.

In addition, in the first embodiment, when the field stop unit 126 rotates about the rotation center 126α and the light receiving unit 130a of the light amount detector 130 coincides with the illumination optical axis O1, the light amount detector 130 detects the light from the main light source 121. An example of detecting the amount of illumination light has been shown. However, the light amount detector 130 does not necessarily have to be provided on the illumination optical axis O1. By providing the light amount detector 130 in the field stop portion 126 and the slit portion 125 of the light shielding member 129 provided at a position optically conjugate with the eye to be inspected E, even at a position slightly deviated from the illumination optical axis O1, Illumination light at a position optically conjugate with the eye E to be examined can be detected. A light quantity substantially equal to the illumination light quantity at the position of the subject's eye E can be detected.

In the second embodiment, the mirror 126g that totally reflects incident light is provided in the field stop portion 126 of the light shielding member 129, and all the light on the illumination optical axis O1 is reflected toward the light amount detector 130A. . However, the mirror provided on the light blocking member 129 is not limited to this, and may be a mirror that reflects part of the light on the illumination optical axis O1.

Furthermore, in the second embodiment, the illumination light is led to the light amount detector 130A via the mirror 126g, but the present invention is not limited to this. For example, one end of an optical fiber may be arranged on the light shielding surface 126a of the field diaphragm 126, and the light amount detector 130A may be arranged near the other end of the optical fiber. That is, scattered light on the illumination optical axis O1 may be captured from the end face of this optical fiber, and the amount of illumination light at a position optically conjugate with the eye E to be examined may be detected.

10, 10B: ophthalmic device 12: illumination system 13: observation system 30: laser treatment system 126g: mirror 129: light shielding member 125: slit section 126: field stop section 126a: light shielding surfaces 130, 130A, 130B: light amount detector E: Eye to be examined O1: illumination optical axis O2: observation optical axis O3: reflection optical axis (reflection optical path)
O4: treatment optical axis O52: separation optical axis (separation optical path)

Claims (3)

an illumination system that irradiates illumination light toward an eye to be inspected;
an observation system for observing or photographing reflected light from the subject's eye;
and a light intensity detector that detects the light intensity of the illumination light,
The illumination system has a light shielding member arranged at a position optically conjugate with the eye to be inspected and partially shielding the light flux of the illumination light,
The ophthalmologic apparatus, wherein the light amount detector is provided on the light shielding member and is provided at a position for detecting the amount of light at a position optically conjugated to the eye to be examined. an illumination system that irradiates illumination light toward an eye to be inspected;
an observation system for observing or photographing reflected light from the subject's eye;
a light intensity detector for detecting the light intensity of the illumination light;
a laser treatment system that irradiates the eye to be examined with treatment light;
a light separating member arranged at a position where the therapeutic light and the illumination light are combined and optically conjugate with the eye to be examined, and which separates the combined light of the therapeutic light and the illumination light into a plurality of lights; , and
The ophthalmologic apparatus , wherein the light quantity detector is provided on the separated optical path of the light separation member and at a position for detecting the quantity of light at a position optically conjugate with the eye to be examined . 3. The ophthalmologic apparatus according to claim 1 , wherein the light amount detector is provided at a position for detecting the light amount on the optical axis of the illumination light .

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