JP2017039018A - Ophthalmological observation device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ophthalmological observation device capable of observing an eye to be examined using illumination light with visibility characteristics close to natural light.SOLUTION: An ophthalmological observation device includes: an illumination system including a color rendering property conversion filter for enhancing color rendering properties of the light from a white light source and a fluorescent filter for transmitting an excited wavelength component of a fluorescent agent; an observation system for observing an eye to be examined; and a driving unit for arranging the color rendering property conversion filter and the fluorescent filter in an optical path of the illumination system exclusively to each other. The wavelength characteristics of the white light source indicate a steep first peak at a wavelength of approx. 460 nm in the wavelength range of 400-700 nm, and a gentle second peak at a wavelength of approx. 550 nm, which is lower than the first peak. The color rendering property conversion filter includes a color conversion filter configured so that transmissivity monotonously increases for the increase in the wavelength in the wavelength range of 400-700 nm.SELECTED DRAWING: Figure 4A

Description

  The present invention relates to an ophthalmologic observation apparatus.

  The ophthalmologic observation apparatus is an apparatus used for observing an eye to be examined. Ophthalmic observation devices include a slit lamp microscope and a surgical microscope. The slit lamp microscope is an ophthalmologic apparatus that acquires an image of a cross section of the cornea by cutting a light section of the cornea using slit light. The surgical microscope is used for obtaining an enlarged image of the eye to be examined in ophthalmic surgery.

  These ophthalmic observation devices are also used for fluorescence observation. For fluorescence observation, a band-pass filter that transmits a wavelength component that excites a fluorescent agent or a band-pass filter that transmits a wavelength component of generated fluorescence is used.

  Conventionally, a halogen lamp has been used as a light source of an ophthalmic observation apparatus. However, a light source using a high-intensity white light-emitting diode (white LED) as a light source has recently appeared.

JP 2011-004877 A Special table 2011-528592 gazette

  However, since the output light of the high-intensity white LED contains only a small amount of wavelength component (excitation wavelength component, about 490 nm) necessary for fluorescence, a sufficient amount of fluorescence cannot be obtained. In addition, the high-intensity white LED generally has a low color rendering property, and the color of the illumination target (the eye to be examined) becomes unnatural.

  On the other hand, although the above problem can be solved by using a white LED having high color rendering properties that sufficiently includes an excitation wavelength component, this type of white LED has a relatively low luminance and is not suitable as a light source for an ophthalmic observation apparatus. . In particular, it is difficult to perform fluorescence observation that requires a sufficient amount of illumination light using a high color rendering white LED.

  In this way, it is desirable to use a light source with sufficient brightness in fluorescence observation, and in other observation modes, it is desirable to use a light source with high color rendering that has a visual characteristic close to that of natural light. I couldn't be satisfied.

  An object of the present invention is to provide an ophthalmologic observation apparatus capable of observing an eye to be examined using illumination light having visual characteristics close to natural light.

  Another object of the present invention is to provide an ophthalmologic observation apparatus that can use illumination light with high brightness in fluorescence observation and can use illumination light with visual characteristics close to natural light in other observation modes. There is.

  The ophthalmic observation apparatus according to the embodiment includes an illumination system, an observation system, and a drive unit. The illumination system includes a white light source having a light emitting element, a color rendering conversion filter that enhances the color rendering of the light output from the white light source, and a fluorescent filter that transmits the excitation wavelength component of the fluorescent agent administered to the eye to be examined. . The observation system has a configuration for observing the eye to be examined illuminated by the illumination system. The drive unit arranges the color rendering property conversion filter and the fluorescence filter in the light path of the illumination system mutually exclusively. Further, the illumination system illuminates the eye to be examined with light transmitted through the color rendering property conversion filter or the fluorescence filter. The wavelength characteristic of the white light source has a sharp first peak at a wavelength of about 460 nm and a second peak that is gradual and lower than the first peak at a wavelength of about 550 nm in the wavelength range of 400 nm to 700 nm. The color rendering property conversion filter includes a color conversion filter configured so that the transmittance monotonously increases as the wavelength increases in the wavelength range of 400 nm to 700 nm.

  According to the present invention, it is possible to observe the eye to be inspected using illumination light having visual characteristics close to natural light.

  In addition, according to the present invention, illumination light with high luminance can be used in fluorescence observation, and illumination light with visual characteristics close to natural light can be used in other observation modes.

It is a schematic diagram showing an example of composition of an ophthalmology observation device concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmology observation device concerning an embodiment. It is a schematic block diagram showing an example of composition of an ophthalmic observation device concerning an embodiment. It is a schematic explanatory drawing of an example of a structure of the ophthalmic observation apparatus which concerns on embodiment. It is a schematic explanatory drawing of an example of a structure of the ophthalmic observation apparatus which concerns on embodiment.

  An example of an embodiment of an ophthalmologic observation apparatus according to the present invention will be described in detail with reference to the drawings. 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, the slit lamp microscope to which the present invention is applied will be described in detail, but the same configuration can be applied to other ophthalmic observation apparatuses (such as a surgical microscope).

  First, the direction is defined. The direction from the lens (objective lens) located closest to the subject in the apparatus optical system to the subject is defined as the front direction, and the opposite direction is defined as the rear direction. The horizontal direction orthogonal to the front direction is the left-right direction. Furthermore, the direction orthogonal to both the front-rear direction and the left-right direction is defined as the up-down direction.

[Appearance configuration]
The external configuration of the ophthalmic observation apparatus (slit lamp microscope) according to this embodiment will be described with reference to FIG. A computer 100 is connected to the slit lamp microscope 1. The computer 100 performs various control processes and arithmetic processes. Instead of providing the computer 100 separately from the microscope main body (housing for storing the optical system or the like), a configuration in which the same computer is mounted on the microscope main body can be applied.

  The slit lamp microscope 1 is placed on a table 2. The computer 100 may be installed on another table or in another place. The base 4 is configured to be movable in the horizontal direction via the moving mechanism unit 3. The base 4 is moved by tilting the operation handle 5.

  A support portion 15 that supports the observation system 6 and the illumination system 8 is provided on the upper surface of the base 4. A support arm 16 that supports the observation system 6 is attached to the support unit 15 so as to be rotatable in the left-right direction. A support arm 17 that supports the illumination system 8 is attached to an upper portion of the support arm 16 so as to be rotatable in the left-right direction. The support arms 16 and 17 are independently coaxially rotatable.

  The observation system 6 is moved by manually rotating the support arm 16. The illumination system 8 is moved by manually rotating the support arm 17. In addition, each support arm 16 and 17 may be comprised so that it may be rotated by an electrical mechanism. In that case, an actuator for generating a driving force for rotating the support arms 16 and 17 and a transmission mechanism for transmitting the driving force are provided. The actuator is constituted by, for example, a stepping motor (pulse motor). The transmission mechanism is constituted by, for example, a combination of gears, a rack and pinion, or the like.

  The illumination system 8 irradiates the eye E with illumination light. As described above, the illumination system 8 can swing in the left-right direction around the pivot shaft extending in the up-down direction. Thereby, the irradiation direction of the illumination light to the eye E is changed. The illumination system 8 may be configured to swing in the vertical direction. That is, you may be comprised so that the elevation angle and depression angle of illumination light can be changed.

  The observation system 6 has a pair of left and right optical systems that guide reflected light of illumination light from the eye E. This optical system is housed in the barrel main body 9. The end of the lens barrel body 9 is an eyepiece 9a. The examiner looks at the eye E with the naked eye by looking into the eyepiece 9a. As described above, the lens barrel body 9 can be rotated in the left-right direction by rotating the support arm 16. Thereby, the direction of the observation system 6 with respect to the eye E can be changed. Note that the reflected light of the illumination light includes various kinds of light passing through the eye E such as scattered light, for example, and these various kinds of light are referred to as “reflected light”.

  A chin rest 10 is disposed at a position facing the lens barrel body 9. The chin rest 10 is provided with a chin rest 10a and a forehead rest 10b for stably arranging the face of the subject.

  An observation magnification operation knob 11 for changing the observation magnification is disposed on the side surface of the barrel main body 9. Further, an imaging device 13 for photographing the eye E is connected to the barrel main body 9. The imaging device 13 includes an imaging element. The imaging element is a photoelectric conversion element that detects light and outputs an electrical signal (image signal). The image signal is input to the computer 100. As the imaging element, for example, a CCD (Charge Coupled Device) image sensor or a CMOS (Complementary Metal Oxide Semiconductor) image sensor is used. A mirror 12 that reflects the illumination light beam output from the illumination system 8 toward the eye E is disposed below the illumination system 8.

[Configuration of optical system]
The configuration of the optical system of the slit lamp microscope 1 will be described with reference to FIG. The slit lamp microscope 1 has an observation system 6 and an illumination system 8.

[Observation system]
The observation system 6 includes a pair of left and right optical systems. The left and right optical systems have substantially the same configuration. The examiner can observe the eye E with binoculars using the left and right optical systems. In FIG. 2, only one of the left and right optical systems of the observation system 6 is shown. Reference numeral O <b> 1 is an optical axis (observation optical axis) of the observation system 6.

  Each of the left and right optical systems of the observation system 6 includes an objective lens 31, a variable magnification optical system 32, a diaphragm 33, a relay lens 35, a prism 36, and an eyepiece lens 37. The beam splitter 34 is provided in only one or both of the left and right optical systems. The eyepiece lens 37 is provided in the eyepiece 9a. A symbol P indicates an imaging position of light guided to the eyepiece lens 37. Reference sign Ec represents the cornea of the eye E, reference sign Ep represents the iris, and reference sign Er represents the fundus. Reference Eo indicates the examiner's eye.

  The variable magnification optical system 32 includes a plurality of (for example, two) variable magnification lenses 32a and 32b. The variable power lenses 32a and 32b are movable along the observation optical axis O1. Thereby, the magnification (field angle) of the naked eye observation image of the eye E and the captured image can be changed. The magnification is changed by operating the observation magnification operation knob 11. Moreover, you may comprise so that a magnification may be electrically changed using a switch etc. which are not illustrated.

  The beam splitter 34 divides the light traveling along the observation optical axis O1 into two. The light transmitted through the beam splitter 34 is guided to the examiner's eye Eo via the relay lens 35, the prism 36 and the eyepiece lens 37. The prism 36 includes two optical elements 36a and 36b, and translates the traveling direction of light upward.

  On the other hand, the light reflected by the beam splitter 34 is guided to the imaging element 43 of the imaging device 13 through the relay lens 41 and the mirror 42. The image sensor 43 detects the reflected light and generates an image signal.

  A barrier filter 83 is disposed between the variable magnification optical system 32 and the beam splitter 34. The barrier filter 83 is provided so as to be removable from the optical path (observation optical path) of the observation system 6. The barrier filter 83 is inserted into the observation optical path when performing fluorescence observation. The barrier filter 83 is an optical filter (bandpass filter) that transmits a wavelength component corresponding to the fluorescence emitted by the fluorescent agent administered to the eye E during fluorescence observation. A mechanism for moving the barrier filter 83 will be described later.

[Lighting system]
The illumination system 8 includes a white light source 51, a relay lens 52, an illumination diaphragm 56, a condenser lens 53, a field diaphragm 57, a slit (slit) forming unit 54, and a condenser lens 55. In addition, an optical filter, which will be described later, is disposed between the slit forming portion 54 and the condenser lens 55. This optical filter is provided so as to be detachable with respect to the optical path of the illumination system 8 (illumination optical path). A symbol O2 indicates the optical axis of the illumination system 8 (illumination optical axis).

  The white light source 51 outputs illumination light. The white light source 51 has a light emitting element (light emitting diode). As such a white light source 51, there is a white LED. Some of them use a light emitting element as a backlight, such as a white organic EL light source. In general, a white light source is a light source that outputs light having a spectral distribution over almost the entire visible region or a light source that outputs light in a predetermined wavelength band having a predetermined wavelength as a central wavelength, and the output light is substantially It is visually recognized as white. In this embodiment, it is assumed that the white light source 51 is a cold white light source. The cold white light source is a white light source that outputs light having a relatively low color temperature. The cold-colored white light source is applied particularly when a color temperature conversion filter described later is used.

  Note that a light source different from the white light source 51 can be additionally provided. For example, a light source that outputs steady light and a light source that outputs flash light can be provided separately. In addition, a light source for corneal observation and a light source for fundus observation can be provided separately.

  The slit forming unit 54 is used to generate slit light (slit light). The slit forming part 54 has a pair of slit blades. The width of the slit light is changed by changing the interval between the slit blades (slit width).

  The illumination stop 56 is configured to be able to change the size of the translucent portion, and acts to limit the amount of light emitted from the white light source 51 to the eye E to be examined. That is, the illumination stop 56 is an optical member for changing the brightness of the illumination light applied to the eye E. The illumination stop 56 also has functions such as reducing the reflection of illumination light by the cornea Ec and the crystalline lens, and adjusting the brightness of the illumination light.

  The field stop 57 is configured to be able to change the size of the translucent portion, and acts to limit the irradiation field of the light output from the white light source 51 to the eye E. The translucent part of the field stop 57 is formed in a circular shape, for example.

  An optical filter disposed between the slit forming part 54 and the condenser lens 55 will be described. This optical filter includes at least a color rendering conversion filter. Further, a color temperature conversion filter and a fluorescent filter may be included. When two or more optical filters are provided, each optical filter can be inserted into and removed from the illumination optical path.

  The color rendering conversion filter is an optical filter that enhances the color rendering of the light output from the white light source 51. “Improve color rendering” means that the color rendering conversion filter converts the output light of the white light source 51 into light having a spectral distribution closer to natural light.

  The color temperature conversion filter is an optical filter that reduces the color temperature of the light output from the white light source 51. As described above, when a color temperature conversion filter is used, a cold white light source is used as the white light source 51. The color temperature conversion filter acts to convert cold color light output from the cold color white light source into warmer color light.

  The fluorescence filter is an optical filter (bandpass filter) that transmits a wavelength component (excitation wavelength component) that excites a fluorescent agent administered to the eye E and generates fluorescence, and is also called an exciter filter.

  In this embodiment, a color rendering property conversion filter, a color temperature conversion filter, and a fluorescence filter are provided. Furthermore, in this embodiment, the color rendering conversion filter and the color temperature conversion filter are configured as a single optical filter. The optical filter having the two functions may be referred to as a color conversion filter. Therefore, in this embodiment, the illumination system 8 is provided with two optical filters (color conversion filters) having a color rendering conversion function and a color temperature conversion function, and optical filters (fluorescence filters) used in fluorescence observation. Although details will be described later, the color conversion filter and the fluorescence filter are arranged exclusively in the illumination light path.

  In FIG. 2, the color conversion filter is denoted by reference numeral 81 and the fluorescent filter is denoted by reference numeral 82. The color conversion filter 81 is inclined with respect to the illumination optical axis O2. That is, the color conversion filter 81 is arranged such that the normal direction of the light incident surface (and the light emitting surface) forms a predetermined angle with respect to the illumination optical axis O2. This inclination angle is, for example, 10 degrees. Such an inclined arrangement can prevent light reflected by the color conversion filter 81 from being mixed into the illumination light and affecting the color characteristics of the illumination light.

[Control system configuration]
A control system of the slit lamp microscope 1 will be described with reference to FIG. The control system of the slit lamp microscope 1 is configured around the control unit 101. Note that FIG. 3 shows only components that are particularly focused on in this embodiment, and other components are omitted.

[Drive system]
The control system of the slit lamp microscope 1 includes a drive system that drives various members. This drive system includes a slit drive unit 54A related to the illumination system 8, an illumination stop drive unit 56A, a field stop drive unit 57A and a filter drive unit 80A, and a filter drive unit 83A related to the observation system 6. Each drive unit includes an actuator such as a pulse motor or a solenoid. Further, the drive unit may include a transmission mechanism that transmits the driving force generated by the actuator.

  The slit driving unit 54A functions to change the slit blade width by moving the pair of slit blades of the slit forming unit 54. The slit driving unit 54A is an example of a “fourth driving unit”.

  The illumination stop driving unit 56A functions to operate the illumination stop 56 to change the amount of illumination light applied to the eye E. The illumination stop driving unit 56A is an example of a “fifth driving unit”.

  The field stop driving unit 57A functions to change the irradiation light field of the illumination light for the eye E by operating the field stop 57. The field stop drive unit 57A is an example of a “sixth drive unit”.

  The filter driving unit 80A functions to insert and remove these optical filters with respect to the illumination optical path by driving the filter holding member 80 that holds the color conversion filter 81 and the fluorescent filter 82. The filter driving unit 80A is an example of a “first driving unit”, a “second driving unit”, and a “third driving unit”. The filter holding member 80 is, for example, a disk-shaped member in which the optical filters are fitted in an arrangement along the circumferential direction, and a turret (filter disk) configured to be rotatable around its central axis. It is. In that case, the filter driving unit 80A is, for example, a pulse motor that generates a driving force for rotating the turret around the central axis.

  The filter driving unit 83A related to the observation system 6 functions to insert and remove the barrier filter 83 with respect to the observation optical axis O1. The filter driving unit 83A includes, for example, a solenoid that generates a linear driving force. When an optical filter is provided in addition to the barrier filter 83, a configuration including a turret and a pulse motor similar to those described above can be applied.

(Control part)
The control unit 101 controls each unit of the slit lamp microscope 1. For example, the control unit 101 controls the observation system 6 and the illumination system 8. Control of the observation system 6 includes control of the observation magnification by the variable magnification optical system 32, control of the aperture size of the diaphragm 33, control of the charge accumulation time, sensitivity, frame rate, etc. of the image sensor 43, and insertion / removal of the barrier filter 83. There is control. The insertion / removal control of the barrier filter 83 is performed by controlling the filter driving unit 83A.

  Further, the illumination system 8 is controlled by controlling the output intensity of light by the white light source 51 (dimming control), controlling the aperture size (irradiation light amount) of the illumination aperture 56, and adjusting the aperture size (irradiation field) of the field aperture 57. Control, slit width control by the slit forming unit 54, and insertion / removal control of the optical filters (the color conversion filter 81 and the fluorescent filter 82). Dimming control of the white light source 51 includes amplitude control and pulse width control. In the amplitude control, the intensity of output light is changed by controlling the applied current value to the LED. In the pulse width control, the applied current to the LED is turned on / off at a constant frequency, and the intensity of the output light is changed by changing the ratio of the on time. The opening size of the illumination stop 56 is controlled by controlling the illumination stop driving unit 56A. The aperture size of the field stop 57 is controlled by controlling the field stop drive unit 57A. Control of the slit width by the slit forming section 54 is performed by controlling the slit driving section 54A. Control of insertion / removal of the optical filter is performed by controlling the filter driving unit 80A.

  The control unit 101 is provided with a storage unit 102. Various types of information are stored in the storage unit 102. The control unit 101 performs a process for reading data stored in the storage unit 102 and a process for writing data to the storage unit 102.

  The control unit 101 includes a microprocessor, a RAM, a ROM, a hard disk drive, and the like. This hard disk drive stores a control program in advance. The operation of the control unit 101 is realized by the cooperation of this control program and the hardware.

  The control unit 101 is disposed in the apparatus main body (for example, in the base 4) of the slit lamp microscope 1 or the computer 100.

[Display section]
The display unit 103 displays various information under the control of the control unit 101. The display unit 103 includes an arbitrary display device such as a flat panel display such as an LCD or a CRT display. The display unit 103 may be provided in the apparatus main body of the slit lamp microscope 1 or may be provided in the computer 100.

(Operation section)
The operation unit 104 includes an operation device and an input device. The operation unit 104 includes buttons and switches (for example, the operation handle 5) provided on the apparatus main body, a mouse of the computer 100, a keyboard, and the like. It is also possible to use any operation device or input device such as a trackball, a dedicated operation panel, a switch, a button, or a dial.

  In FIG. 3, the display unit 103 and the operation unit 104 are illustrated separately, but they can be configured integrally. As a specific example, a touch panel LCD can be used.

[About wavelength characteristics of white light source and optical filter]
Here, the wavelength characteristics of the white light source 51 and the color conversion filter 81 will be described. A graph F in FIG. 4A shows an example of the wavelength characteristic (filter characteristic) of the color conversion filter 81. The filter characteristics F of the color conversion filter 81 are set in a wavelength range of about 400 nm to 700 nm, which is a visible light band. The transmittance of the color conversion filter 81 monotonously increases with an increase in wavelength. More specifically, the transmittance is about 20% near the wavelength of 400 nm, and the transmittance gradually increases up to near the wavelength of 500 nm. The transmittance around a wavelength of 500 nm is about 30%. Further, the filter characteristic F increases steeply from a wavelength of about 500 nm to a wavelength of about 600 nm. The transmittance around the wavelength of 600 nm is about 90%. The transmittance gradually increases from about 600 nm to 700 nm, and finally reaches 100%.

  FIG. 4B shows the relative intensity as a function of wavelength. A one-dot chain line graph L indicates the wavelength characteristics (spectral distribution) of the output light from the white light source 51. A solid line graph T indicates the wavelength characteristics (spectral distribution) of the output light transmitted through the color conversion filter 81. A broken line graph B shows the wavelength characteristics (spectral distribution) of the output light from the halogen lamp. The halogen lamp is a white light source with high color rendering properties.

  The wavelength characteristic L of the white light source 51 is set in a wavelength range of about 400 nm to 700 nm, has a steep peak near the wavelength of 460 nm, and a gentle peak near the wavelength of 550 nm. Note that light having a wavelength of about 450 nm to 500 nm in the vicinity of the steep peak corresponds to an excitation wavelength component of the fluorescent agent.

  In this embodiment, the wavelength characteristic B of the halogen lamp is used as a target of the wavelength characteristic of illumination light obtained by the combination of the white light source 51 and the color conversion filter 81. Actually, the wavelength characteristic T of the illumination light obtained by the combination of the wavelength characteristic L of the white light source 51 and the filter characteristic (transmission characteristic) F of the color conversion filter 81 approximates the wavelength characteristic B of the halogen lamp.

  As described above, the white light source 51 outputs high intensity light in the excitation wavelength component of the fluorescent agent. In addition, by combining the white light source 51 and the color conversion filter 81, high color rendering light close to a halogen lamp is generated. Specifically, by using the color conversion filter 81, the average color rendering index is improved from about 70 to 80 or more, and the color temperature is reduced from about 6500K to about 3500K. Further, assuming that the amount of fluorescence by the halogen lamp and the fluorescence filter is 100%, the combination of the white light source 51 and the fluorescence filter 82 (color), while the amount of fluorescence is about 41% in the combination of the warm color LED and the fluorescence filter. The conversion filter 81 is retracted from the illumination optical path) and becomes 179%.

[control]
Control executed by the slit lamp microscope 1 will be described. In addition, it is possible to arbitrarily combine two or more of the control examples described below.

(First control example)
The controller 101 exclusively inserts the color conversion filter 81 and the fluorescence filter into the illumination optical path. Specifically, for example, when an instruction to start fluorescence observation is given using the operation unit 104, the control unit 101 controls the filter driving unit 80A to retract the color conversion filter 81 from the illumination optical path and 82 is inserted into the illumination light path. In addition to this control, the control unit 101 can control the filter driving unit 83A to insert the barrier filter 83 into the observation optical path.

  Further, when an instruction to end fluorescence observation (instruction to start normal observation) is given, the control unit 101 controls the filter driving unit 80A to retract the fluorescent filter 82 from the illumination light path and to change the color conversion filter 81. Insert into the illumination light path. In addition to this control, the control unit 101 can control the filter driving unit 83A to retract the barrier filter 83 from the observation optical path.

  According to this control example, the filter to be used can be automatically switched in response to switching of the observation mode. In the fluorescence observation, the fluorescent filter 82 that transmits the excitation wavelength component of the fluorescent agent is used instead of the color conversion filter 81, and therefore corresponds to the excitation wavelength component of the wavelength characteristic L of the white light source 51 shown in FIG. 4B. The eye E is irradiated with light having a wavelength of about 450 nm to 500 nm. This light has a high intensity (a large amount of light) as described above. On the other hand, in the observation mode other than the fluorescence observation, the color conversion filter 81 is used instead of the fluorescence filter 82, and thus the eye E is irradiated with the light having the wavelength characteristic T of the illumination light shown in FIG. This light is light with high color rendering properties close to a halogen lamp as described above.

(Second control example)
Upon receiving the instruction to start fluorescence observation, the control unit 101 controls the filter driving unit 80A to insert the fluorescent filter 82 into the illumination optical path, and controls the slit driving unit 54A to control a pair of slits in the slit forming unit 54. Increase the blade spacing. At this time, the slit width can be maximized.

  According to this control example, the slit width is automatically enlarged in conjunction with the shift to fluorescence observation. Therefore, it is possible to automatically increase the intensity (light quantity) of light (excitation light) irradiated to the eye E in fluorescence observation, and to obtain a sufficient fluorescence amount.

(Third control example)
Upon receiving the instruction to start fluorescence observation, the control unit 101 controls the filter driving unit 80A to insert the fluorescent filter 82 into the illumination optical path, and controls the illumination stop driving unit 56A to increase the aperture size of the illumination stop 56. As a result, the amount of illumination light applied to the eye E is increased. At this time, the opening size of the illumination stop 56 can be maximized.

  According to this control example, the amount of irradiation light is automatically increased in conjunction with the shift to fluorescence observation. Therefore, it is possible to automatically increase the amount of light (excitation light) irradiated to the eye E during fluorescence observation.

(Fourth control example)
Upon receiving the instruction to start fluorescence observation, the control unit 101 controls the filter driving unit 80A to insert the fluorescent filter 82 into the illumination optical path, and controls the field stop driving unit 57A to increase the aperture size of the field stop 57. By doing so, the irradiation field of the illumination light to the eye E is expanded. At this time, the aperture size of the field stop 57 can be maximized.

  According to this control example, the irradiation field is automatically expanded in conjunction with the shift to the fluorescence observation. Therefore, the observation range in the fluorescence observation can be automatically expanded.

(Fifth control example)
Upon receiving the instruction to start fluorescence observation, the control unit 101 controls the filter driving unit 80A to insert the fluorescent filter 82 into the illumination optical path, and controls the white light source 51 (that is, the applied current from the power source to the white light source 51). Increase the light output intensity.

  According to this control example, the intensity of light output from the white light source 51 is automatically increased in conjunction with the shift to fluorescence observation. Therefore, it is possible to automatically increase the intensity (light quantity) of light (excitation light) irradiated to the eye E in fluorescence observation.

  It should be noted that by combining the second to fifth operation examples, it is possible to greatly increase the amount of fluorescence obtained by fluorescence observation or expand the observation range. Further, in response to the transition from the fluorescence observation to another observation mode, it is possible to perform the reverse control to the second to fifth operation examples. That is, in response to the transition from the fluorescence observation to another observation mode, the slit width can be reduced, the amount of irradiation light can be reduced, the irradiation field can be reduced, and the output intensity of the white light source 51 can be reduced.

[Action / Effect]
The operation and effect of the slit lamp microscope 1 will be described.

  The slit lamp microscope 1 has an illumination system 8 and an observation system 6. The illumination system 8 includes a white light source 51 and a color rendering property conversion filter (color conversion filter 81), and illuminates the eye E with light transmitted through the color rendering property conversion filter. The white light source 51 has a light emitting element, and is, for example, a white LED or a white organic EL light source. The color rendering property conversion filter (color conversion filter 81) acts to enhance the color rendering property of the light output from the white light source 51. The observation system 6 has an optical system for observing the eye E illuminated by such an illumination system 8.

  According to such a slit lamp microscope 1, the eye E can be observed using illumination light having visual characteristics close to natural light by a combination of the white light source 51 and the color rendering property conversion filter (color conversion filter 81). Is possible.

  The slit lamp microscope 1 has a first drive unit (filter drive unit 80A) that inserts and removes a color rendering conversion filter (color conversion filter 81) with respect to the optical path of the illumination system 8.

  Even if a cold white light source is applied as the white light source 51 and the illumination system 8 includes a color temperature conversion filter (color conversion filter 81) for reducing the color temperature of the light output by the cold white light source. Good. Thereby, it is possible to use illumination light having suitable color characteristics as described above. The slit lamp microscope 1 has a second drive unit (filter drive unit 80A) that inserts and removes the color temperature conversion filter with respect to the optical path of the illumination system.

  In this embodiment, the color rendering property conversion filter and the color temperature conversion filter are configured as a single optical filter, but they can also be configured as separate optical filters. In that case, the two optical filters can be configured to be inserted into and removed from the illumination optical path independently.

  The illumination system 8 may include a fluorescent filter 82 that transmits the excitation wavelength component of the fluorescent agent administered to the eye E. Thereby, fluorescence observation becomes possible. The slit lamp microscope 1 has a third drive unit (filter drive unit 80A) for inserting and removing the fluorescent filter 82 with respect to the optical path of the illumination system.

  The slit lamp microscope 1 links the insertion of the color rendering property conversion filter (color conversion filter 81) into the illumination optical path and the withdrawal of the fluorescence filter 82 from the illumination optical path, and the insertion of the fluorescence filter 82 into the illumination optical path. A first control unit (control unit 101) that controls the first drive unit and the third drive unit (both filter drive units 80A) so that the rendition of the color rendering property conversion filter (color conversion filter 81) from the illumination optical path is linked. ). Thereby, it is possible to easily switch between fluorescence observation and another observation mode.

  The first control unit (control unit 101) interlocks the insertion of the color rendering property conversion filter and the color temperature conversion filter (both color conversion filter 81) into the illumination optical path and the withdrawal of the fluorescent filter 82 from the illumination optical path, and The first drive unit and the third drive unit (both of which are coupled with insertion of the fluorescent filter 82 into the illumination optical path and retraction of the color rendering property conversion filter and the color temperature conversion filter (both color conversion filter 81) from the illumination optical path). The filter driver 80A) can be controlled. Thereby, it is possible to easily switch between fluorescence observation and another observation mode.

  The color rendering conversion filter and the color temperature conversion filter are configured as a single optical filter (color conversion filter 81), and the first drive unit and the second drive unit are configured as a single drive unit (filter drive unit 80A). can do. Thereby, simplification of the device configuration (configuration of the optical system) can be achieved.

  Further, a holding member (filter holding member 80) for holding a single optical filter (color conversion filter 81) and the fluorescent filter 82 is provided, and the first driving unit, the second driving unit, and the third driving unit are provided. It can be configured as a single drive unit (filter drive unit 80A) that moves the holding member. Thereby, simplification of an apparatus structure can be achieved.

  When the ophthalmic observation apparatus according to the present invention is configured as a slit lamp microscope, the illumination system 8 is provided with a pair of slit blades (slit forming portions 54) that generate slit light from the light output from the white light source 51. Further, the third driving is performed so that the fourth driving unit (slit driving unit 54A) that changes the interval (slit width) of the slit blades and the insertion of the fluorescent filter 82 in the illumination optical path and the enlargement of the slit blade interval are linked. It is possible to provide a second control unit (control unit 101) that controls the unit (filter drive unit 80A) and the fourth drive unit (slit drive unit 54A). Thereby, when shifting to fluorescence observation, the intensity (light quantity) of light (excitation light) irradiated to the eye E can be automatically increased.

  An illumination stop 56 that restricts the amount of light emitted from the white light source 51 and applied to the eye E can be provided in the illumination system 8. Further, a fifth drive unit (illumination diaphragm drive unit 56A) that changes the amount of light emitted by the illumination diaphragm 56 and a third drive unit (filter drive) so that the insertion of the fluorescent filter 82 in the illumination optical path and the increase in the amount of irradiated light are linked. Unit 80A) and a third control unit (control unit 101) for controlling the fifth driving unit (illumination stop driving unit 56A). Thereby, it is possible to automatically increase the amount of light (excitation light) irradiated to the eye E during the transition to fluorescence observation.

  The illumination system 8 can be provided with a field stop 57 that limits the irradiation field of the light output from the white light source 51 to the eye E to be examined. Further, a sixth drive unit (field drive unit 57A) that changes the irradiation field by the field stop 57, and a third drive unit (filter drive) so that the insertion of the fluorescent filter 82 in the illumination optical path and the expansion of the irradiation field are linked. Part 80A) and a fourth drive part (control part 101) for controlling the sixth drive part (field stop drive part 57A). This makes it possible to automatically expand the irradiation field of light (excitation light) for the eye E during the transition to fluorescence observation.

  A third drive unit (filter drive unit 80A) and a fifth control unit (control unit) that controls the white light source 51 so that the insertion of the fluorescent filter 82 into the illumination optical path and the increase in the light output intensity by the white light source 51 are linked. 101). Thereby, when shifting to fluorescence observation, the intensity (light quantity) of light (excitation light) irradiated to the eye E can be automatically increased.

  The color rendering property conversion filter (color conversion filter 81) can be inclined with respect to the optical axis of the illumination system 8. Thereby, it is possible to prevent the reflected light from the color rendering property conversion filter (color conversion filter 81) from being mixed into the illumination light and affecting the color characteristics of the illumination light.

  According to this embodiment, illumination light with high luminance can be used in fluorescence observation, and illumination light with visual characteristics close to natural light can be used in other observation modes.

  The configuration described above is merely a specific example for carrying out the present invention. A person who intends to implement the present invention can appropriately make arbitrary modifications within the scope of the gist of the present invention.

1 slit lamp microscope (ophthalmic observation device)
6 Observation System 8 Illumination System 51 White Light Source 54 Slit Forming Unit 54A Slit Driving Unit 56 Illumination Diaphragm 56A Illumination Diaphragm Driving Unit 57 Field Diaphragm 57A Field Diaphragm Driving Unit 80 Filter Holding Member 80A Filter Driving Unit 81 Color Conversion Filter 82 Fluorescent Filter 83 Barrier filter 83A Filter drive unit 100 Computer 101 Control unit 102 Storage unit 103 Display unit 104 Operation unit O1 Observation optical axis O2 Illumination optical axis E Eye to be examined

Claims (3)

An illumination system comprising: a white light source having a light emitting element; a color rendering conversion filter that enhances color rendering of the light output from the white light source; and a fluorescent filter that transmits an excitation wavelength component of a fluorescent agent administered to the eye to be examined. ,
An observation system for observing the eye to be examined illuminated by the illumination system;
A driving unit that arranges the color rendering property conversion filter and the fluorescent filter in the optical path of the illumination system exclusively;
Have
The illumination system illuminates the subject's eye with light transmitted through the color rendering property conversion filter or the fluorescent filter,
The wavelength characteristic of the white light source has a sharp first peak at a wavelength of about 460 nm and a second peak at a wavelength of about 550 nm that is gentle and lower than the first peak in a wavelength range of 400 nm to 700 nm.
The ophthalmic observation apparatus, wherein the color rendering property conversion filter includes a color conversion filter configured such that the transmittance monotonously increases with an increase in wavelength in a wavelength range of 400 nm to 700 nm. The transmittance of the color conversion filter monotonically increases from about 20% at a wavelength of about 400 nm to about 30% at a wavelength of about 500 nm, monotonically increases from about 30% at a wavelength of about 500 nm to about 90% at a wavelength of about 600 nm. The ophthalmic observation apparatus according to claim 1, wherein the ophthalmic observation apparatus is configured to monotonically increase from about 90% at about 600 nm to 100% at a wavelength of about 700 nm. The white light source is a white light emitting diode;
The said color conversion filter is comprised so that the spectral distribution of the light output from the said white light emitting diode may be converted into the spectral distribution close | similar to the spectral distribution of a halogen lamp. The ophthalmologic observation apparatus described in 1.