JP3512823B2 - Ophthalmic medical equipment - Google Patents

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ophthalmic medical device, and more particularly to an ophthalmic medical device for photocoagulating the fundus of the eye.

[0002]

2. Description of the Related Art Conventionally, there has been known a technique for performing photocoagulation of a fundus with a laser photocoagulation device having a configuration combined with a slit lamp microscope.

[0003]

In the conventional photocoagulation apparatus as described above, because of corneal reflection due to illumination light, etc.,
The field of view of the fundus that can be observed is almost slit-shaped and fairly narrow.

For this reason, it is difficult to quickly identify a diseased site obtained from a color fundus photograph or a photograph of a wide field of view by fluorescence angiography, and it is necessary to move the field of view one after another according to the spread of the affected area. Yes, considerable skill and skill was required.

Therefore, a first object of the present invention is to scan a fundus image by a scanning laser ophthalmoscope on a monitor screen.
Wide field of view equivalent to that obtained with a check-type laser ophthalmoscope
A large display and a clear fundus image can be used to easily identify the diseased part, and at the same time, the position of the spot image of the treatment laser light can be accurately displayed in color over the fundus image for safe and efficient treatment. Another object of the present invention is to provide an ophthalmologic medical device which is easy to operate by unitizing each unit of the apparatus and which can be configured easily and inexpensively.

In order to solve the first problem, it is conceivable to combine a scanning laser ophthalmoscope with a laser photocoagulator having a wavelength different from that of the observation laser beam.

The scanning laser ophthalmoscope has an advantage that the observation laser light is irradiated with being narrowed down and thus has a deep depth of focus and a sharp fundus image can be obtained even in rough focusing.

On the other hand, the therapeutic laser beam concentrates energy on the focal plane for photocoagulation, and before and after that, a cone angle of about 10 degrees is usually provided in order to disperse the energy. Therefore, the treatment laser light needs to be more precisely focused on the fundus image that is roughly focused by the observation laser light.

Further, when the cross section of the fundus of the eye is enlarged, they are composed of several layers such as the retinal surface layer, the retinal nerve fiber layer, the retinal pigment epithelium layer, and the choroid, which are reached by the wavelength of the illuminating laser beam. It is already known that the layers (or reflective surfaces) to be applied are different.

For example, He--N is used as an observation laser light source.
When using an e laser and an argon laser as a therapeutic laser light source, a He-Ne laser (632 nm) is a choroid and an argon laser (blue 488 nm, green 514 nm).
nm) will be reflected near the surface of the retina.

That is, there is a difference in thickness between the focal plane of the observation laser beam and the focal plane of the therapeutic laser beam only by the thickness of the layer. Therefore, it is necessary to have a function of focusing by the therapeutic laser light actually used for photocoagulation instead of the observation laser light.

[0012] Therefore, a second object of the present invention is to provide an ophthalmologic medical device capable of more precisely adjusting the focus of therapeutic laser light.

[0013]

In order to solve the above-mentioned problems, the present invention has a basic structure in which a scanning laser ophthalmoscope is combined with a laser photocoagulator having a wavelength different from that of an observation laser beam. used, the light amount for illuminating the different therapeutic laser light wavelength and the observation laser beam onto the eye
Together Placing the split member forward or backward of the objective lens
In addition, the therapeutic laser light is detected behind the pinhole arranged behind the two-dimensional deflection scanning device for the observation laser light .
A light-receiving element is placed, and the light-receiving signal is input to the signal processing device and synthesized so as to be superimposed on the fundus image, and the position of the spot image is displayed on the monitor, or the therapeutic laser is used.
Is placed in the optical path of the light source so that it can be inserted and removed,
Provided with detection means for detecting the focus state of the medical laser light
The spot image position and focus match status are displayed on the monitor.
Or in addition, the light component that reflects the therapeutic laser light
Place the split member in front of the objective lens and
Laser photocoagulator part including laser light source and other parts
It has a structure that allows it to be attached and detached .

[0014]

[Operation] According to the above configuration, the therapeutic laser for photocoagulation
-Two-dimensional deflection scanning of laser light for observation of spot image of light
A receiver placed behind a pinhole located at the rear of the device.
Scanning laser that can be detected in real time by an optical element
ー Scanning image on the monitor screen
The same wide field of view as that obtained with the ophthalmoscope
At the same time, it is possible to easily identify the diseased site with a clear fundus image.
In addition, the position of the spot image of the therapeutic laser beam should be aligned with the fundus image.
Colors can be displayed accurately on top of each other for safe and efficient treatment.
You can follow.

Further, a light component that reflects the therapeutic laser light
By placing the split member in front of the objective lens,
Laser photocoagulator including laser light source for other parts
It can be removable with respect to the minute .

Further, the deviation of the spot image from the focal plane due to the therapeutic laser light can be detected, and the therapeutic laser light can be aimed extremely accurately.

[0017]

【Example】

<First Embodiment> A first embodiment will be described below with reference to the drawings. A scanning laser ophthalmoscope is combined with a laser photocoagulator having a wavelength different from that of the observation laser beam.

In FIG. 1, a laser beam 2 from an observation laser light source (eg, He-Ne laser) 1 passes through a hole 11a of a perforated mirror 11 and is condensed by a lens 3 (the perforated mirror 11 is a half mirror. May be replaced).

Further, the laser light is reflected by the horizontal scanning polygon mirror 4. This horizontal scanning polygon mirror 4
Is directly connected to the motor 5 and scans the laser beam in the horizontal direction (direction perpendicular to the paper surface) by high-speed rotation of the horizontal scanning polygon mirror 4.

Further, the laser light passes through the lens 6, is reflected by the vertical scanning mirror 7 driven by the galvanometer 8, and is transmitted through the half mirror 26. At this time, the horizontal scanning polygon mirror 4 and the vertical scanning mirror 7 are arranged in an optically substantially conjugate relationship with respect to the lens 6.

The high speed rotation of the motor 5 and the vibration of the galvanometer 8 are both driven and controlled by the signal processing device 18.

The laser light transmitted through the half mirror 26 passes through the objective lens 9 and the iris (pupil) 10b of the eye 10 to be inspected.
And is focused on the fundus 10a.

At this time, the vertical scanning mirror 7 and the iris (pupil)
10b and the objective lens 9 are arranged in an optically substantially conjugate relationship. Therefore, the laser light always enters through the center of the pupil 10b and scans the fundus.

The laser light reflected by the fundus 10a passes through the pupil 10b in a fully spread state, passes through the objective lens 9 and the half mirror 26, and is passed through the vertical scanning mirror 7, the lens 6, the horizontal scanning polygon mirror 4, and the lens. To 3,
The incident light travels in the same optical path as the opposite direction, is reflected on the outside of the hole 11a of the perforated mirror 11, and is condensed on the pinhole 13 by the lens 12.

Since the lens system is arranged as described above, the laser beam 2 of the observing laser light source 1 passes through the two-dimensional deflection scanning device, is focused on the fundus 10a, and is two-dimensionally scanned. While holding the information from, the light travels in the same optical path as the incident light in a state where the light spreads outward from the incident light, the direction is changed by the perforated mirror 11, and the light is always focused on the pinhole 13.

Since harmful light such as scattered light generated from other than the condensing point of the fundus 10a cannot pass through this pinhole 13, such a lens system can obtain a good fundus image.

At this time, the eye to be inspected 10 also constitutes a part of the above-mentioned lens system, and thus it is necessary to adjust the diopter correction, the interval, and the optical axis alignment with respect to the eye to be inspected.

The reflected light from the fundus passing through the pinhole 13 is configured so that the observation laser light is transmitted by the dichroic mirror 14 and the therapeutic laser light is reflected, and the former is reflected by the light receiving element 15 and the latter is detected by the latter. Light receiving element 1
Detect at 7.

In this embodiment, the dichroic mirror is arranged behind the pinhole, but the pinhole does not change its function even if it is arranged between the dichroic mirror and each light receiving element, and it can be implemented. is there.

Further, instead of the dichroic mirror, a band pass filter for selectively passing the observation laser beam and the treatment laser beam may be arranged in front of the half mirror and each light receiving element, but the cost is increased. Leads to.

A protective filter 1 is provided in front of the light receiving element 17.
6 is arranged so that it can be inserted into and removed from the optical path, and protects the light receiving element from the powerful therapeutic laser light.

On the other hand, the laser beam 21 of the therapeutic laser light source (for example, an argon laser) 20 is a neutral density filter 2 which is removably arranged in the optical path of the laser beam.
2. After passing through the telescope 23, it is reflected by the scan mirror 24 and further reflected by the half mirror 26,
An image is formed on the fundus 10a through the central portion of the objective lens 9 and the pupil 10b of the subject's eye.

The neutral density filter 22 is always inserted in the optical path so as to weaken the therapeutic laser light and use it for aiming the therapeutic light.

The operation of inserting and removing the neutral density filter is performed by the light receiving element 17
Associated with a protective filter 16 located in front of the. That is, when the fire button (not shown) is turned on, the protection filter 16 is inserted into the optical path, and the neutral density filter 22
Is withdrawn from the optical path, and the therapeutic laser light is increased to perform photocoagulation treatment. The neutral density filter 22 returns to the optical path after retracting for a predetermined time. When the restoration is completed, the protection filter retracts and the detection action of the therapeutic laser light is restarted.

The telescope 23 forms a spot at the exit end of the therapeutic laser light source on the fundus through the objective lens, and at the same time, a part of the lens constituting the telescope is moved in the optical axis direction by a cam (not shown) or the like. It has a function of converting the size of the spot image formed on the fundus by moving to.

The spot size converting function is, for example, in the photocoagulation treatment of diabetic retinopathy (proliferative type), the spot size is 200 μm in the posterior pole excluding the macula and its surroundings.
m, and further, the peripheral part is changed to 500 μm and the outermost part is changed to 500 to 1000 μm, which is useful for efficient treatment.

The scan mirror 24 is connected to the micromanipulator 25, and by operating the micromanipulator, the scan mirror can be swung to move the spot image to an arbitrary position on the fundus.

The scan mirror and the iris (pupil) 10
b is arranged at a position that is substantially conjugate with respect to the objective lens 9. Therefore, the therapeutic laser light always passes through the center of the pupil 10b and irradiates the fundus.

The therapeutic laser light reflected by the fundus spreads through the pupil as shown by the thick broken line, passes through the objective lens 9 and the half mirror 26, and follows the same optical path as the reflected laser light for observation. Proceed and reach pinhole 13.

However, when the position of the observation laser beam is different from the position of the spot image of the therapeutic (aiming) laser beam, the therapeutic laser beam does not pass through the pinhole as shown in FIG. It passes through the pinhole only when the position and the position of the spot image match.

That is, the position of the spot image is detected when the spot image moved to an arbitrary position by the swing of the scan mirror 24 and the converging position of the observation laser beam are scanned and coincide with each other. become. At the same time, the size of the spot image can be known by detecting the coincidence of time.

With the above configuration, the light receiving element 15 detects the reflected light of the observation laser light, and the light receiving element receives the reflected light of the spot image of the therapeutic (aiming) laser light passing through the pinhole 13. 17 and the signal processing device 18
To enter. Image processing is performed together with the drive control signals of the motor 5 and the galvanometer 8, and the position and size of the spot image are monitored so as to be superimposed on the fundus image.
To display.

At this time, if a color monitor is used and a color of the same system as the wavelength of the laser beam for treatment is used, the display of the spot image becomes clearer and the treatment can be performed efficiently.

Specifically, the fundus (retina) is composed of several layers such as the retinal surface layer, the retinal nerve fiber layer, the retinal pigment epithelium layer, and the choroid, and the layer to reach depends on the wavelength of the laser light to be irradiated. Laser light is selected according to the condition to be treated. In the case of the present invention, when a He-Ne laser (wavelength 633 nm) is used as an observation laser light source, argon blue (488n) having a wavelength sufficiently different from that of the He-Ne laser is used as a therapeutic laser light.
m), argon green (514 nm), DYE yellow (577 nm), DYE orange (590n)
It is possible to incorporate m) or the like for selective use. At this time, the spot image position and size on the monitor
For convenience of operation, the color is displayed in the same system color as the wavelength of the selected laser beam.

FIG. 2 shows a case in which a half mirror 27 that reflects the laser beam for treatment is arranged in front of the objective lens 9. In this case, as shown in the figure, a lens 26 'is provided instead of the objective lens 9 in the optical path of the therapeutic laser light.

That is, the telescope 23 and the lens 2
With 6 ', it has a function of forming a spot at the exit end of the therapeutic laser light source on the fundus and changing the size of the spot image.

Further, the scan mirror 24 and the iris (pupil) 10b are arranged at positions which are substantially conjugate with each other with respect to the lens 26 '.

Therefore, in the configuration of FIG. 2, the laser light always passes through the center of the pupil and forms an image on the fundus even if the scan mirror 24 swings.

According to the above configuration, the laser photocoagulation device can be attached or detached without impairing the function of the scanning laser ophthalmoscope located behind the objective lens 9. Therefore, the laser photocoagulator can be easily and inexpensively configured based on the existing scanning laser ophthalmoscope, and the laser photocoagulator part to be supplied as an option can be easily attached and detached. .

In addition, in the configuration of FIG. 2 as well, it is possible to easily identify the diseased part with the clear fundus image as described above, and at the same time, the position of the spot image of the therapeutic laser light can be displayed in color by overlapping with the fundus image. Can be treated efficiently.

<Second Embodiment> A second embodiment of the present invention is shown in FIG. 3 and thereafter. In the following, description of the same parts as those in the first embodiment will be omitted.

In this embodiment, the optical system of the therapeutic laser is different from that of the first embodiment.

In FIG. 3, a laser beam 21 of a therapeutic laser light source (for example, an argon laser) 20 passes through a neutral density filter 22 and a telescope 23 which are removably arranged in the optical path of the laser beam, and a circle. The plurality of small holes 28a, 28b (see FIG. 4) of the plate 28 form a plurality of fine beams, which are reflected by the scan mirror 24,
Passes through the focus lens 26 ', and then the half mirror 2
7, the objective lens 9 and the pupil 10b of the eye to be examined.
An image is formed on the fundus 10a through the central part of the.

At the time of aiming, the neutral density filter 22 and the disc 28 are inserted in the optical path of the laser beam so as to weaken the therapeutic laser light and use it as the aiming light.

The operation of inserting and removing the neutral density filter 22 and the disk is performed by the protection filter 16 arranged in front of the light receiving element 17.
Is related to.

These operations are performed by turning on a fire button (not shown), and after inserting the protective filter 16 into the optical path, the neutral density filter 22 and the disk 28 are respectively withdrawn from the optical path, so that the therapeutic laser light is entirely discharged. After passing through, the amount of light is increased and photocoagulation treatment is performed.

The neutral density filter 22 and the disk 28 are returned to the optical path after being retracted for a predetermined time. Disk 28 and reduced
The insertion / removal of the optical filter 22 is controlled by the signal processing device 18.

When the restoration of the neutral density filter 22 and the disk 28 is completed, the protective filter 16 is retracted and the detection function of the therapeutic laser light is restarted.

Similar to the first embodiment, other functions, for example, the position and size of the spot image can be displayed on the monitor 19 so as to be superposed on the fundus image to improve the aiming and displaying performance.

Next, the focus detection mechanism of the therapeutic laser light will be described.

As in the present embodiment (or the first embodiment), the scanning laser ophthalmoscope has a deep focal depth because the beam of the laser light for observation is narrowed and irradiated, and even in rough focusing. A sharp fundus image is obtained.

However, focusing is necessary as a correction for the diopter of the eye to be examined. The therapeutic laser beam concentrates energy on the focal plane where photocoagulation is performed, disperses the energy before and after the focal plane, and usually a cone angle of about 10 degrees is used so that the photocoagulation does not reach outside the treatment site. It is provided.

That is, if the therapeutic laser is out of focus, the energy is dispersed and the desired photocoagulation is not performed.

Therefore, in order to focus the therapeutic laser light more precisely on the fundus image that is roughly focused by the observation laser light, a focus detection mechanism for detecting a deviation from the image plane of the fundus. Is required.

Further, enlarging the cross section of the fundus, they are composed of several layers such as the retinal surface layer, retinal nerve fiber layer, retinal pigment epithelium layer, and choroid, which are reached by the wavelength of the laser beam to be irradiated. It is well known that different layers (or reflective surfaces) are used.

Therefore, it is necessary to have a function of focusing with the therapeutic laser light used for photocoagulation, instead of focusing by looking at the fundus image with the observation laser light.

In this embodiment, since the therapeutic laser beam is provided with a cone angle of about 10 degrees as shown in FIG. 5, the spot size naturally becomes large when the image is formed in front of the focal plane. However, on the other hand, the energy of the laser beam disperses according to the area ratio, the desired energy density cannot be obtained, and photocoagulation becomes insufficient.

In FIGS. 3 and 4, the small hole 28 of the disk 28 is shown.
The plurality of aiming lights 21a and 21b that have passed through a and 28b are
Focus lens 26 ′, objective lens 9 and eye 1 to be inspected
An image is formed on the fundus 10a by the light collecting function of 0 itself. At this time, if the image plane (for example, the surface layer of the retina) and the focal plane coincide with each other, the spot image is displayed as one spot image on the monitor with a plurality of beams completely overlapping as shown in the figure.

In FIG. 6, a plurality of aiming lights 21a, 21a
In the case of b, when there is an image plane in front of the focal point 21 ', the spot images are separated as 21a' and 21b 'and are displayed as a plurality of spot images on the monitor.

At this time, the disk 28 is driven by the motor 27 '.
Is rotated at a speed of about 1 rotation / 2 seconds. For example, when the image plane is on the front side or the rear side of the focal plane, the spot image rotates on the monitor and the focal plane and the image plane coincide. When it does, it appears to the examiner that rotation has stopped.

The objective lens 9 or the focus lens 26 'is adjusted while observing the in-focus state on the monitor 19. The laser beam 2 of the observation laser light is focused on the fundus 10a as 2 '.

With the above configuration, it is possible to detect the deviation of the spot image from the focal plane due to the therapeutic laser light, and to avoid the coagulation failure due to the energy dispersion.
Treatment can be reliably performed.

FIGS. 7 and 8 show another configuration in which the aiming beam is divided into two in order to detect the coincidence between the focal plane and the image plane of the therapeutic laser light.

A parallel plate beam splitter 30 is arranged in place of the circular plate 28. A half mirror 30a is provided on one surface of the parallel plate beam splitter 30 and a mirror 30b is provided on the other surface thereof. 21 is divided by a half mirror, a part of which is transmitted to be an aiming beam 21a, and another part of which is reflected by a mirror 30b.
b.

Even with such a method, two aiming beams can be formed without using the disc 28. By rotating the parallel plate beam splitter 30 like the disk 28,
The same operation as described above is possible. The parallel plate beam sp
Like the disk 28, the litter 30 is a neutral density filter for photocoagulation.
At the same time as -22, retract from the optical axis.

[0076]

As is apparent from the above, according to the present invention, the scanning laser ophthalmoscope is provided with a laser beam for observation.
With the combination of laser photocoagulators with different lengths,
A clear view of the fundus with a wide field of view is constantly displayed on the monitor screen.
Take advantage of the advantages of scanning laser ophthalmoscope
After the two-dimensional deflection scanning device for observation laser light
To the light-receiving element placed behind the pinhole
The signal from the fundus of the eye can be detected in real time,
A clear image of the fundus makes it easy to identify the site of disease and at the same time cures it.
Accurately position the spot image of the medical laser light on the fundus image.
It can be displayed in color for easy and safe treatment.
You can Or even more, the optical path of the therapeutic laser source
Laser beam for treatment on the fundus
The position of the spot image
Adopt a configuration that displays the matching status of position and focus on the monitor
The focus of the spot image by the therapeutic laser light
Displacement from the surface can be detected, and therapeutic laser light can reach the fundus.
Aiming and focusing can be done very accurately,
Reliable photocoagulation without solidification failure due to energy dispersion
Can be treated. Or, in addition, a therapeutic label
A light splitting member that reflects laser light is placed in front of the objective lens.
According to the arrangement, a laser including a therapeutic laser light source
-The photocoagulator part must be removable from other parts.
The light splitting member can be removed and the objective lens
Retract from the front and use it as the original scanning laser ophthalmoscope
Can be used as an existing scanning laser detector.
There is an advantage that it can be easily and inexpensively configured by using the one of glasses.
It

[0077]

[Brief description of drawings]

FIG. 1 is an explanatory view showing a first embodiment of a photocoagulation device adopting the present invention.

FIG. 2 is an explanatory diagram showing a modified example of the apparatus of FIG.

FIG. 3 is an explanatory view showing a second embodiment of the photocoagulation device adopting the present invention.

FIG. 4 is an explanatory view showing details of the apparatus of FIG.

5 is an explanatory view showing a cone angle of a therapeutic laser of the apparatus of FIG.

FIG. 6 is an explanatory diagram showing a focusing function of therapeutic light in the apparatus of FIG.

FIG. 7 is an explanatory diagram showing a modified example of the apparatus of FIG.

8 is an explanatory diagram showing a modified example of the apparatus of FIG.

[Explanation of symbols]

1 Laser light source for observation 2 laser beam 3,6,12 lens 4 Horizontal scanning polygon mirror 5 motors 7 Vertical scanning mirror 8 galvanometer 9 Objective lens 10 eye 10a fundus 10b Iris (pupil) 11 perforated mirror 12 lenses 13 pinholes 14 dichroic mirror 15 Light receiving element 16 protection filter 17 Light receiving element 18 Signal processing device 19 monitors 20 therapeutic laser light source 21 laser beam 22 Dark filter 23 Telescope 24 scan mirror 25 Micro Manipulator 26 half mirror 26 'lens 27 Half mirror 27 'motor 28 discs 30 Parallel plate beam splitter

─────────────────────────────────────────────────── ─── Continuation of the front page (72) Inventor Koji Nakanishi, 3-14-14 Nihonbashihonmachi, Chuo-ku, Tokyo Kowa Co., Ltd., Electro-Optical Division (56) Reference JP-A-2-161944 (JP, A) Kai 61-2851 (JP, A) JP 55-10984 (JP, A) JP 2-271820 (JP, A) (58) Fields investigated (Int.Cl. ⁷ , DB name) A61F 9 / 007 A61B 3/10 A61B 18/20

Claims (13)

(57) [Claims] 1. A method for observing, diagnosing or treating the fundus of an eye to be examined.
In an ophthalmologic device used for this purpose, an observation laser light source having a predetermined wavelength and a laser light from the observation laser light source are two-dimensionally polarized.
Optical means for scanning in the direction, and the observation laser light scanned by the optical means
Objective lens for projecting to the bottom and observation from the fundus
For receiving the reflected light of the laser light for use in photoelectric conversion
1 of the light receiving element, and the therapeutic laser light source having a wavelength different from that of the observation laser beam, the laser beam emitted from the treatment laser source before
Light splitting member arranged in front of or behind the objective lens
A lens system for forming an image on the fundus as a spot image via, and is arranged at a position substantially optically conjugate to the pupil of the eye to be inspected, for moving the spot image to an arbitrary position on the fundus. In front of the scan mirror and to receive the reflected light of the therapeutic laser light from the fundus
A second member arranged behind the pinhole behind the optical means
To the image signal of the fundus output from the first light receiving element.
The therapeutic laser output from the second light receiving element
-A signal processor for superimposing and synthesizing light position signals
A step, and the position of the spot image of the therapeutic laser light is set on the eye of the subject eye.
An ophthalmic medical device characterized by displaying the bottom image on the monitor screen . 2. The ophthalmologic apparatus according to claim 1, wherein a He--Ne laser is arranged as an observation laser light source and an argon laser is arranged as a treatment laser light source. 3. The therapeutic laser light source wherein the lens system is
The laser light emitted from the
Spot size converter for forming a pot image
The ophthalmic medical device according to claim 1 or 2, which has an ability . 4. The first light receiving element and the second light receiving element
The dichroic mirror for separating an optical path is arranged, The ophthalmic medical device according to any one of claims 1 to 3 , wherein . 5. The position of the spot image of the therapeutic laser light
On the monitor screen of the fundus image of the eye to be examined.
The ophthalmic medical device according to any one of claims 1 to 4 , wherein color display is performed according to a wavelength of laser light . 6. A method for observing, diagnosing or treating the fundus of an eye to be examined.
The specified wavelength in ophthalmic medical devices used for
Laser light source for observation having a
Optics for two-dimensional deflection scanning of laser light from a source
Means and the observation laser light scanned by the optical means.
Objective lens for projecting to the bottom and observation from the fundus
For receiving the reflected light of the laser light for use in photoelectric conversion
1 of the light receiving element, and the therapeutic laser light source having a wavelength different from that of the observation laser beam, the laser beam emitted from the treatment laser source before
Light splitting member arranged in front of or behind the objective lens
A lens system for forming an image on the fundus as a spot image through, and is arranged to be removable in the optical path of the therapeutic laser light source,
Detects the focus state of therapeutic laser light on the fundus
A detection means for the subject's eye pupil, are located in an optically substantially conjugate position, and the scan mirror for moving the spot image at an arbitrary position of the fundus reflection of the therapeutic laser light from the retina To receive light
A second member arranged behind the pinhole behind the optical means
To the image signal of the fundus output from the first light receiving element.
The therapeutic laser output from the second light receiving element
-A signal processor for superimposing and synthesizing light position signals
A step, and the position and focus of the spot image of the therapeutic laser light match
An ophthalmic medical device characterized by displaying the condition on the monitor screen of the fundus image of the eye to be examined . 7. The ophthalmic medical device according to claim 6, wherein a He--Ne laser is arranged as the observation laser light source, and an argon laser is arranged as the treatment laser light source. 8. The therapeutic laser light source, wherein the lens system is the therapeutic laser light source.
The light beams emitted from the
Spot size conversion function for forming a dot image
Ophthalmic medical device according to claim 6 or 7, characterized in that it has a. 9. A lens system for forming a spot of therapeutic laser light on the fundus of the eye, and a focal plane of the observation laser light and a therapeutic laser light, separately from the objective lens for correcting the diopter of the eye to be examined. The focus lens is adjustably arranged in order to correct the deviation from the focal plane of the laser beam and to perform the focus adjustment of the therapeutic laser light more precisely than that of the observation laser light. Ophthalmic medical equipment as described. 10. The therapeutic laser is used as the detection means.
Has multiple small holes to split the aiming light of the light source into two
Discs or parallel plates with different reflection characteristics on each surface
The ophthalmic medical device according to claim 6, wherein the ophthalmic medical device is configured by using a beam splitter . 11. A dichroic mirror is arranged in the detection optical path of the therapeutic laser light.
The ophthalmic medical device according to 10. 12. The therapeutic laser light is displayed on a monitor screen to show the matching state of the position and the focus of the spot image formed on the fundus.
The ophthalmic medical equipment according to claims 6 to 11, which is color-displayed according to the wavelength of . 13. A light component that reflects the therapeutic laser light
The split member is arranged in front of the objective lens and
A therapeutic laser light source, the lens system, and the mask
The laser photocoagulator part including the mirror can be replaced with other parts.
The device according to claim 1, wherein the device is detachable from the device.
Alternatively, the ophthalmic medical device according to claim 6.