JP2007117249A - Ophthalmology photography apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To easily adjust the light amount of observation and the light amount of photography while switching photography mode between non-emission light and emission light. <P>SOLUTION: Non-emission and emission light photography are discriminated at a step of S1 just after intravenous injection of a fluorescence agent. When it is non-emission light photography, a photographic barrier filter is sorted at a step of S2. When the filter is inserted with the gain measured at a step of S3: when the gain is lower than 15 dB, judged Non-emission light photography is recognized at a step of S4. When the gain is large, emission light photography is recognized at a step of S5, and the applied voltage and the gain are defaulted at a step of S6 and the operationality is improved in the emission light photography. When emission-light photography is recognized at the step of S1, the filter is sorted at the step of S7, and the applied voltage is measured at the step of S8 as the filter is inserted. When it is lower than 100 V, non-emission light photography is recognized at the step of S9, and the observation initial data is set at the step of S10, and the operationality is improved in the non-emission light photography. When the filter is not inserted or the applied voltage is large, is recognized emission light photography at the step of S11. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to an ophthalmologic photographing apparatus such as a fundus camera capable of fluorescent photographing used in an ophthalmic clinic or the like.

  Conventionally, as shown in Patent Document 1, there is known an ophthalmologic apparatus that can easily adjust the amount of photographing light to an appropriate exposure amount regardless of the decrease even if the amount of fluorescence decreases with time after the start of fluorescence photographing. . In this Patent Document 1, attention is paid to adjusting the amount of observation illumination light when performing focusing and positioning with observation illumination light such as a halogen lamp before photographing, and photographing is performed in conjunction with this light amount adjustment. It has been proposed to automatically adjust the amount of light appropriately.

  In addition, ophthalmologic photographing apparatuses that generally perform alignment and observation using observation illumination light and perform photographing using a flash light source such as a xenon tube are known, but in recent years, a continuous light source such as a laser light source or a halogen lamp is used. It has been proposed to use an ophthalmologic apparatus that performs both observation and photographing.

  Furthermore, when shooting with a significant change in the appropriate exposure amount, such as fluorescent shooting, a shooting mode using a shooting light source and shooting with a continuous light source without using a shooting light source are performed. An ophthalmologic photographing apparatus for photographing by switching to a non-light emitting photographing mode has also been proposed.

Japanese Patent No. 2808000

  In the conventional example disclosed in Patent Document 1 described above, the amount of photographing light is always increased or decreased at a predetermined increase / decrease ratio in accordance with the adjustment of the amount of observation illumination light. Therefore, it is effective when photographing is performed after focusing and positioning with observation illumination light such as a halogen lamp before photographing. However, if the light amount adjustment operation for the observation illumination light is performed after the completion of the focusing and alignment, there is a problem that the photographing light amount changes without the intention of the examiner.

  In particular, in an apparatus that switches between a flash photography mode that uses a photographic light source and a non-flash photography mode in which photography is performed with observation illumination light without using a photographic light source, the observation illumination is the same as described above in the flash photography mode. When the light amount is adjusted, the photographing light amount increases or decreases. In addition, there is a problem that the amount of photographing light is increased or decreased even for a photographing light source that is not used in the non-light emitting photographing mode.

  In addition, when the conventional example according to Patent Document 1 is not used, there is a problem that when the light emission photographing mode is switched to the light emission photographing mode, the amount of photographing light must be adjusted in a complicated manner.

  An object of the present invention is to provide an ophthalmologic photographing apparatus that can easily adjust the observation light quantity and the photographing light quantity without a sense of incongruity at the time of switching between the non-light-emitting photographing mode and the light emitting photographing mode. It is in.

  Technical features of the ophthalmologic photographing apparatus according to the present invention for achieving the above-mentioned object are: an illumination optical system that includes an observation light source and a photographing light source and illuminates the eye to be examined; an observation optical system that observes the eye to be examined; An imaging optical system for imaging the eye to be examined, an imaging means provided in the observation optical system and the imaging optical system, an observation light quantity input means for setting an observation light quantity by the observation light source, and an observation light quantity input means Observation light quantity control means for adjusting the light quantity of the observation light source, photographing light quantity input means for setting the photographing light quantity by the photographing light source, and photographing light quantity for adjusting the light quantity of the photographing light source connected to the photographing light quantity input means An ophthalmologic photographing apparatus comprising: a control unit; a non-light-emission photographing operation unit that performs photographing using the observation light source; and a photographing operation switching unit that switches a light-emission photographing operation unit that performs photographing using the photographing light source. , By the photographing operation switching means, when performing switching of the non-emitting photographing operation unit light emitting photographing operation unit is to perform the initial setting of the light amount control by the observation light amount control unit or the imaging light amount control means.

  According to the ophthalmologic photographing apparatus according to the present invention, the initial setting of the photographing light amount is performed, and the photographing light amount does not increase or decrease in accordance with the adjustment of the observation illumination light amount. Further, since the initial setting of the observation illumination light amount is performed even in the non-light emission photographing mode in which the adjustment of the observation illumination light amount is mainly performed without using the photographing light source, the observation illumination light amount can be easily adjusted.

  The present invention will be described in detail based on the embodiments shown in the drawings.

  FIG. 1 shows a configuration diagram of a fundus camera in the present embodiment. A fundus illuminating optical system is provided that extends from the observation light source 1 formed of a halogen lamp to the objective lens 2 that is disposed facing the eye E to be examined. In this fundus illumination optical system, a condenser lens 3, a photographic light source 4 comprising a strobe tube, a mirror 5, a diaphragm 6 having a ring-shaped opening, an ICG exciter filter 7a, a lens 8, and a perforated mirror 9 are arranged. ing. Further, instead of the ICG exciter filter 7a inserted in the optical path at the time of near-infrared fluorescent photography, the optical path length correction glass 7b has the same thickness as the filter 7a and is inserted into the optical path at the time of color photography. A visible fluorescent exciter filter 7c is provided. These filters 7a and 7c and glass 7b are inserted into the optical path according to near-infrared fluorescence photography, color photography, and visible fluorescence photography.

  On the optical path behind the perforated mirror 9, a visible fluorescent barrier filter 10a, a photographing lens 11, an imaging lens 12, a quick return mirror 13, and a camera mount 15 incorporating an image sensor 14 having sensitivity in the visible region are sequentially provided. The fundus photographing optical system is arranged.

  Further, instead of the visible fluorescent barrier filter 10a, the optical path length correction glass 10b having the same thickness as the barrier filter 10a and used for color photographing and ICG photographing can be inserted and removed.

  In addition, in the reflection direction of the quick return mirror 13, a mirror 16, a field lens 17, an ICG imaging barrier filter 18 a, a focus lens 19, and an imaging device 20 having sensitivity in the near infrared are sequentially arranged to provide fundus observation imaging optical technology. The system is configured. An ICG observation barrier filter 18b can be inserted instead of the ICG imaging barrier filter 18a. The ICG observation barrier filter 18b is inserted at the time of ICG observation, and the transmission wavelength region is slightly wider than that of the ICG imaging barrier filter 18a. Further, a barrier filter detection means 21 is provided for detecting which of the ICG imaging barrier filter 18a and the ICG observation barrier filter 18b is in the optical path.

  The image sensors 14 and 20 are connected to an amplification factor changing unit 31, and the amplification factor changing unit 31 is connected to a control unit 32, a monitor 33 for displaying an image, and a memory 34.

  Further, the control unit 32 includes an observation light amount input unit 35 that sets the light amount of the observation light source 1 and the gain of the image sensor 14, and a photographing light amount input unit that sets the light amount of the photographing light source 4 and the gain of the image sensor 14. 36, a photographing switch 37 is connected. Further, an observation light source dimming unit 38 and an imaging light source dimming unit 39 are connected to the control unit 32, respectively. The observation light source dimming unit 38 is connected to the observation light source 1, and the imaging light source dimming unit 39 is an imaging unit. The light source 4 is connected.

  When the quick return mirror 13 jumps up and leaves the optical path, a visible fundus photographing optical system is configured by the imaging element 14 having sensitivity in the visible region. Further, when the quick return mirror 13 is inserted in the optical path, a near-infrared fundus observation photographing optical system by the image sensor 20 having sensitivity in the near infrared is configured.

  The image output signals of the image sensors 14 and 20 are input to the amplification factor changing unit 31, and the amplification factor changing unit 31 performs amplification processing on the image output signal in accordance with an instruction from the control unit 32, and displays it on the monitor 33. The image is stored in the memory 34.

  FIG. 2 is a block circuit configuration diagram, and an observation light quantity control unit 32 a is provided in the control unit 32. The observation light amount control unit 32a includes an observation initial data storage unit 32b that stores the light amount and amplification factor of the observation light source 1 in the non-light-emitting photographing mode, and a photographing operation determination unit that determines whether the light-emitting photographing mode or the light-emitting photographing mode. 32c and the imaging | photography light quantity control part 32d are connected. The photographing light amount control unit 32d is connected to a photographing initial data storage unit 32e that stores the light amount and amplification factor of the photographing light source 4 even in the light emission photographing mode.

  An observation light source dimming means 38 and an observation light amount input unit 35 provided outside the control unit 32 are connected to the observation light amount control unit 32a. The observation light quantity input unit 35 is provided with two switches 35a and 35b on the left and right sides and an observation light quantity display LED 35c.

  Further, the output of the amplification factor changing means 31 is connected to the observation light quantity control unit 32a and the photographing light quantity control unit 32d. The output of the filter detection unit 21 is connected to the control unit operation determination unit 32c, and the output of the photographing light source dimming unit 39 and the output of the photographing light amount input unit 36 are connected to the photographing light amount control unit 32d. The photographing light quantity input unit 36 is provided with two switches 36a, 36b and a photographing light quantity display LED 36c.

  When adjusting the light quantity and amplification factor of the photographic light source 4 using the photographic light quantity input unit 36, when the switches 36a and 36b are operated, the photographic light quantity display LEDs 36c are changed and displayed stepwise from F1 to F8. The setting value by the photographing light quantity input unit 36 is detected by the photographing light quantity control unit 32d. The photographing light quantity control unit 32d sets the charging voltage of the capacitor of the photographing light source dimming means 39 and the amplification factor of the amplification factor changing means 31 according to the following Table 1.

Table 1
Imaging light quantity input unit 36 Amplification factor changing means 31 to capacitor
Set value of applied voltage gain
F1 53V 0dB
F2 75V 0dB
F3 106V 0dB
F4 150V 0dB
F5 212V 0dB
F6 300V 0dB
F7 300V 6dB
F8 300V 12dB

  However, the amplification factor at this time is set after an input from the photographing switch 37 as will be described later. That is, the control unit 32 that has detected that the setting value of the photographing light amount input unit 36 is F1, for example, sets the applied voltage of the capacitor inside the photographing light source dimming unit 39 to 53 V, and the amplification factor changing unit 31 Record that the gain is 0 dB. Similarly, when it is detected that the set value of the photographing light quantity input unit 36 is F7, the applied voltage of the capacitor is set to 300 V, and it is recorded that the amplification factor of the amplification factor changing means 31 is 6 dB.

  In order to adjust the light amount and the amplification factor of the observation light source 1 by the observation light amount input unit 35, when the two switches 35a and 35b are operated, the observation light amount display LED 35c is changed and displayed stepwise from 1 to 9. The set value by the observation light quantity input unit 35 is detected by the observation light quantity control unit 32a, and the observation light quantity control unit 32a controls the applied voltage to the observation light source 1 and the amplification factor of the amplification factor changing means 31 according to Table 2. To do.

Table 2
Observation light quantity input unit 35 Amplification factor changing means 31 for observation light source 1
Set value of applied voltage gain
1 0V 0dB
2 2V 0dB
3 4V 0dB
4 8V 0dB
5 16V 0dB
6 16V 6dB
7 16V 12dB
8 16V 18dB
9 16V 24dB

  That is, when the scale of the observation light quantity input unit 35 indicates, for example, 3, the applied voltage to the observation light source 1 is 4V, and the amplification factor of the amplification factor changing means 31 is 0 dB. When the scale of the observation light quantity input unit 35 is 5, the applied voltage is 16 V and the amplification factor is 0 dB. Further, when the scale of the observation light quantity input unit 35 is 7, the applied voltage remains 16V and the amplification factor is 12 dB. When the scale is 9, the applied voltage remains 16V and is amplified. The rate is 24 dB.

  As described above, the observation light quantity input unit 35 is adjusted, and the eyepiece Er of the eye E to be examined is observed with appropriate brightness, and the alignment with the eye E and the photographing lens 11 are moved using an operating means (not shown). Use to focus and check the shooting range.

  When performing color imaging, the optical path length correction glass 7b is inserted into the fundus illumination optical system, and the optical path length correction glass 10b is inserted into the fundus observation imaging system, and the quick return mirror 13 jumps up and retracts out of the optical path. Since the reflectance of the fundus Er with respect to visible light is high, the setting adjustment range of the observation light quantity input unit 35 is limited to 1 to 5, and the amplification factor is not changed. Then, the control unit 32 that has detected the input to the photographing switch 37 starts light accumulation in the image sensor 14, transmits a light emission signal to the photographing light source light control means 39, and the photographing light source 4 that has received the light emission signal takes a photograph. Light is emitted by the electric charge stored in the capacitor inside the light source light control means 39.

  The luminous flux emitted from the imaging light source 4 passes through the aperture of the diaphragm 6 having a ring-shaped aperture in the same manner as the observation light, passes through the lens 8, and is reflected leftward by the mirror portion around the perforated mirror 9. 2 illuminates the fundus Er through the pupil Ep of the eye E to be examined. The thus illuminated image of the fundus Er passes through the objective lens 2, the photographing lens 11, and the imaging lens 12 again, forms an image on the image sensor 14, and is converted into an electrical signal. The amplification factor changing means 31 does not perform amplification processing on these signals, records the photographed image in the memory 34, and displays the fundus image on the monitor 33.

  Next, in the case of performing ICG imaging, a mydriatic agent is instilled, and the subject is seated with the dilated eye E toward the objective lens 2. Then, the ICG exciter filter 7a and the ICG observation barrier filter 18b are inserted into the optical path.

  In such a configuration, light emitted from the observation light source 1 passes through the same optical path as described above, and only the near-infrared light illuminates the fundus Er with the ICG exciter filter 7a. The fundus image illuminated in this way is reflected by the quick return mirror 13, passes through the ICG observation barrier filter 18b, forms an image on the image sensor 20, and is converted into an electrical signal. These electric signals are input to the amplification factor changing means 31 and amplified to a predetermined amplification factor, and an image based on this signal is displayed on the monitor 33.

  Here, since the ICG observation barrier filter 18b has a wide transmission wavelength region as described above, the state of the fundus Er can be observed by the monitor 33 even when no fluorescence is emitted. The examiner observes the fundus image reflected on the monitor 33 and operates the observation light quantity input unit 35 so that the fundus image has a brightness that is easy to see. The examiner looks at the fundus image displayed on the monitor 33, confirms that the alignment and focus are good, and then intravenously injects the fluorescent agent to the subject and starts photographing. At the same time, a fluorescence timer for recording the elapsed time after the intravenous injection of the fluorescent agent is started, and the ICG imaging barrier filter 18a is inserted into the optical path to wait for the appearance of the fluorescence image.

  As shown in FIG. 3, since the fluorescence luminance changes depending on the time after intravenous injection, the examiner looks at the observed fluorescence image and the fluorescence image photographed by the photographing switch 37, and observes the observation light amount input unit 35 and the photographing light amount input. The unit 36 is operated.

  FIG. 3 shows an example of photographing. When the fluorescence luminance changes remarkably, photographing is performed by operating the observation light quantity input unit 35, and when the fluorescence luminance is stabilized and gradually decreases, photographing is performed. This is a case where the light amount input unit 36 is operated to perform photographing. Note that section A is a non-flash photography mode, and section B is a flash photography mode.

  When performing such ICG imaging, the examiner sets the setting value of the observation light quantity input unit 35 to 7, waits for the appearance of the fluorescent image, and sets the setting value of the observation light quantity input unit 35 until time T after intravenous injection. Is operated between 4 and 7. When the setting value of the observation light quantity input unit 35 is set to 8 at time T and the setting value of the observation light quantity input unit 35 is fixed to 8 after time T, the imaging light quantity input unit 36 is operated between F3 and F8. Explained as an example.

  FIG. 4 shows the relationship between the setting value of the observation light amount input unit 35 and the setting value of the photographing light amount input unit 36, and shows that the photographing light amount corresponding to 18 dB of the amplification factor is equivalent to F3. Normally, the correlation between the amplification factor and the photographing light amount varies depending on the ophthalmologic apparatus, but here, the photographing light amount corresponding to 18 dB of the amplification factor is described as being equivalent to F3.

  FIG. 5 shows an operation flowchart of internal processing of the control unit 32. This internal processing is performed when the ICG photographing barrier filter 18a is inserted into and removed from the optical path, and the setting value of the observation light amount input unit 35 or the setting value of the photographing light amount input unit 36 is changed.

  Immediately after the intravenous injection of the fluorescent agent, in step S1 of FIG. 5, the photographing operation determining unit 32c determines whether the light emitting photographing mode or the light emitting photographing mode. Since the non-light-emitting shooting mode is set as the initial value of the shooting operation, the process proceeds to step S2, and the barrier filter detection means 21 determines whether or not the ICG shooting barrier filter 18a is inserted. In this case, since the ICG imaging barrier filter 18a is inserted in the optical path, the process proceeds to step S3. In step S3, it is determined whether or not the amplification factor is lower than 15 dB. However, since the set value of the observation light quantity input unit 35 is 7, and the amplification factor of the amplification factor changing unit 31 is 12 dB according to Table 2, Proceeding to step S4, it is determined that the light-emitting shooting mode is selected.

  Until the time T after intravenous injection, the set value of the observation light quantity input unit 35 is operated between 4 and 7, and the ICG imaging barrier filter 18a remains inserted in the optical path. During this time, the observation light quantity control unit 32a controls the amplification factor of the amplification factor changing unit 31 from 0 dB to 12 dB and the applied voltage of the observation light source dimming unit 38 to the observation light source 1 between 8V to 16V according to Table 2. .

  In addition, when photographing is performed by the photographing switch 37 during this time, an image picked up by the imaging element 20 with the illumination light from the observation light source 1 is recorded in the memory 34 with the amplification factor set by the amplification factor changing means 31. . In the image recorded in the memory 34, the fundus image displayed on the monitor 33 at the time of observation is recorded as it is. Further, even if the photographing light quantity input unit 36 is operated during this time, the non-light emission photographing mode is maintained, so that the setting of the observation light quantity control unit 32a is not changed by the operation of the photographing light quantity input unit 36.

  Next, when the setting value of the observation light quantity input unit 35 is set to 8 at time T, the shooting operation determination unit 32c is in the non-light emission shooting mode as step S1 in FIG. . In step S2, the barrier filter detection means 21 determines whether or not the ICG imaging barrier filter 18a is inserted. Since the ICG imaging barrier filter 18a is inserted in the optical path, the process proceeds to step S3. In step S3, it is determined whether or not the gain is lower than 15 dB. However, since the set value of the observation light quantity input unit 35 is 8, the gain of the gain changing means 31 is 18 dB according to Table 2. Therefore, the process proceeds to step S5. In step S5, the shooting operation determination unit 32c determines that the flash shooting mode is selected, and the process proceeds to step S6.

  In step S6, the photographing initial data storage unit 32e is read by the photographing light amount control unit 32d. The initial photographing data storage means 32e has the same setting as the setting value F3 of the photographing light amount input unit 36 as indicated by the arrow A → B shown in FIG. Accordingly, the photographic light quantity control unit 32d changes the setting value of the photographic light quantity input unit 36 to F3, sets the applied voltage of the capacitor of the photographic light source dimming means 39 from Table 1 to 106 V, and changes the amplification factor changing means 31 at the time of photographing. The amplification factor is 0 dB.

  The operation in step S6 is a characteristic control of the present invention, and the value set in the photographing light amount input unit 36 before the execution of step S6 is ignored. In this case, it is always set to F3. The

  If the setting value of the photographing light amount input unit 36 is F8 without performing the control in step S6 as in the prior art, the setting value of the observation light amount input unit 35 can be recorded with 7 until just before time T. Despite this, the flash photography mode is entered at the moment when the setting value of the observation light quantity input unit 35 is set to 8. Therefore, the voltage applied to the condenser of the photographing light source dimming means 39 is set to 300 V, and the amplification factor of the amplification factor changing means 31 at the time of photographing is 12 dB. Light increases. As a result, the amount of light clearly exceeds, and the setting of the photographing light amount input unit 36 needs to be set to a low value.

  Assuming that the set value of the photographing light quantity input unit 36 is F1, the light emission photographing mode is set at time T, and the applied voltage of the capacitor of the photographing light source light control means 39 is set to 53V. Since the amplification factor of the amplification factor changing means 31 at the time of photographing is 0 dB, the illumination light from the photographing light source 4 corresponding to the voltage 53V applied to the capacitor increases, but the amplification factor of the amplification factor changing means 31 is insufficient by 12 dB. As a result, the amount of light is insufficient. For this reason, it is necessary to set the photographing light amount input unit 36 to a high value.

  In this way, when the non-light-emitting shooting mode is changed to the flash shooting mode, the applied voltage and amplification factor of the condenser of the shooting light source dimming means 39 are changed by the shooting light quantity control unit 32d based on the shooting initial data storage means 32e. The means 31 is initialized. Thereby, the operability of the photographing light quantity input unit 36 in the flash photographing mode is greatly improved.

  After time T, the setting value of the observation light quantity input unit 35 is 8, the ICG imaging barrier filter 18a remains inserted in the optical path, and the setting value of the imaging light quantity input unit 36 is between F3 and F8. It is operating with. For this reason, the internal processing of the control unit 32 proceeds to step S7 as the light emission photographing mode based on the determination in step S1 of FIG. 5, and the barrier filter detection unit 21 determines whether or not the ICG photographing barrier filter has been inserted. Do. Since the ICG imaging barrier filter 18a is inserted in the optical path, the process proceeds to step S8, and it is determined whether or not the applied voltage of the capacitor of the imaging light source dimming means 39 is lower than 100V. Since the set value of the photographing light quantity input unit 36 is F3 to F8, the process proceeds to step S11, and the photographing operation determining unit 32c determines the light emission photographing mode.

  During this time, when the photographing switch 37 is pressed to perform photographing, the gain changing means 31 sets the illumination light from the observation light source 1 and the image picked up by the imaging element 20 by the illumination light from the photographing light source 4. Is recorded in the memory 34 at the amplification factor. Since the image recorded in the memory 34 is different from the fundus image displayed on the monitor 33 at the time of observation, confirmation is performed by displaying it on the monitor 33 for a predetermined time. The illumination light from the photographing light source 4 at this time and the amplification factor set by the amplification factor changing means 31 are determined by the set value of the photographing light amount input unit 36. Further, when the fluorescence luminance decreases with the passage of time after intravenous injection, it is necessary to increase the photographing light amount by the photographing light amount input unit 36.

  Further, even if the observation light quantity input unit 35 is operated during this time, the light emission photographing mode is maintained, so that the setting of the photographing light quantity control unit 32d is not changed by the operation of the observation light quantity input unit 35.

  In this operation example, after the time T, the photographing light amount input unit 36 is operated between F3 and F8 while the set value of the observation light amount input unit 35 is fixed at 8. When the ICG imaging barrier filter 18a is changed to the ICG observation barrier filter 18b, there is no change in the section A of the non-light emitting imaging mode and the section B of the light emitting imaging mode in FIG.

  Next, as Example 2, when the fluorescence luminance is low as shown in FIG. 6, the ICG observation barrier filter 18b or the imaging light amount input unit 36 is operated to perform imaging, and when the fluorescence luminance is high, the observation light amount The input unit 35 is operated to take a picture.

  When performing such ICG imaging, the examiner operates the observation light quantity input unit 35, waits for the appearance of a fluorescent image with a setting value of 9, and takes the imaging light quantity input unit 36 until time T1 after intravenous injection. Is operated between F3 and F5. At time T1, the setting value of the photographing light quantity input unit 36 is set to F2, and the setting value of the observation light quantity input unit 35 is operated between 3 and 7 from time T1 to T2. At time T2, the ICG observation barrier filter 18b is inserted into the optical path, and after time T2, the photographing light amount input unit 36 is operated between F3 and F8 while the set value of the observation light amount input unit 35 is fixed at 8. In this case, similarly to FIG. 3, the section A shown in FIG. 6 is in the non-flash photography mode, and the section B is in the flash photography mode.

  Immediately after the intravenous injection, as step S1 in FIG. 5, the photographing operation determining unit 32c determines whether the light emitting photographing mode or the light emitting photographing mode. Since the non-light-emitting shooting mode is set as the initial value of the shooting operation, the process proceeds to step S2, and the barrier filter detection means 21 determines whether or not the ICG shooting barrier filter 18a has been inserted. In this case, since the ICG imaging barrier filter 18a is inserted in the optical path, the process proceeds to step S3 to determine whether or not the amplification factor is lower than 15 dB. Since the setting value of the observation light quantity input unit 35 is 9, the amplification factor of the amplification factor changing means 31 is 24 dB according to Table 2, so the process proceeds to step S5, and the shooting operation determination unit 32c determines the light emission shooting mode. move on.

  In step S6, the photographing initial data storage unit 32e is read by the photographing light amount control unit 32d. The initial photographing data storage means 32e has the same setting as the setting value F3 of the photographing light amount input unit 36 as indicated by the arrow A → B shown in FIG. Accordingly, the photographic light quantity control unit 32d changes the setting value F3 of the photographic light quantity input unit 36, sets the applied voltage of the capacitor of the photographic light source dimming means 39 to 106 V from Table 1, and sets the gain changing means 31 of the photographic light source dimming means 39 at the time of photographing. The amplification factor is 0 dB.

  Next, when the setting value of the photographing light quantity input unit 36 is set to F2 at time T1, the photographing operation determination unit 32c is in the flash photographing mode in step S1 of FIG. Accordingly, the process proceeds to step S7, where the barrier filter detection means 21 determines whether or not the ICG imaging barrier filter 18a has been inserted. In this case, since the ICG imaging barrier filter 18a is inserted in the optical path, the process proceeds to step S8 to determine whether or not the applied voltage of the capacitor is lower than 100V. Since the set value of the photographing light quantity input unit 36 is set to F2, and the applied voltage of the capacitor is 75 V from Table 1, the process proceeds to step S9, where the non-light-emitting photographing mode is determined, and the process proceeds to step S10.

  In step S10, the observation initial data storage unit 32b is read by the photographing light quantity control unit 32d. The observation initial data storage means 32b is the same as the set value 7 of the observation light quantity input unit 35 as indicated by the arrow B → A shown in FIG. Therefore, the observation light quantity control unit 32a changes the setting value of the observation light quantity input unit 35 to 7, and the amplification factor of the amplification factor changing unit 31 is 12 dB according to Table 2, and the application of the observation light source dimming unit 38 to the observation light source 1 is applied. The voltage is 16V.

  The operation in step S10 shows the characteristic control of the present invention, similar to the control in step S6. Before step S10 is executed, the set value 9 in the observation light quantity input unit 35 is ignored and is always set to 7.

  When the control in step S10 is not performed as in the prior art, the set value of the observation light quantity input unit 35 is 9, so that the non-light-emitting shooting mode is set at time T1, and the amplification factor changing means 31 performs amplification during shooting. Shooting is performed while the rate is 24 dB. The amount of light is over and the amplification factor is as large as 24 dB, and image degradation occurs. Therefore, it is necessary to set the observation light amount input unit 35 to a low value.

  As described above, when the light emission photographing mode is changed to the non-light emission photographing mode, the voltage applied to the observation light source 1 of the observation light source dimming means 38 by the observation light quantity control unit 32a based on the observation initial data storage means 32b. The amplification factor changing means 31 is initialized. Thereby, the operability of the observation light quantity input unit 35 in the non-light emission photographing mode is improved.

  From time T1 to T2, the setting value of the observation light quantity input unit 35 is operated between 3 and 7, and the ICG imaging barrier filter 18a remains inserted in the optical path. The process proceeds to the non-light emission shooting mode. During this time, the observation light quantity control unit 32a controls the amplification factor of the amplification factor changing means 31 from 0 dB to 12 dB and the applied voltage of the observation light source dimming means 38 to the observation light source 1 between 4 V to 16 V according to Table 2.

  In addition, when photographing is performed by the photographing switch 37 during this time, an image picked up by the imaging element 20 with the illumination light from the observation light source 1 is recorded in the memory 34 with the amplification factor set by the amplification factor changing means 31. . In the image recorded in the memory 34, the fundus image displayed on the monitor 33 at the time of observation is recorded as it is.

  Since the ICG observation barrier filter 18b is inserted into the optical path at time T2, the process proceeds to steps S1 to S6, and is determined to be the flash photography mode. After time T2, the ICG observation barrier filter 18b is inserted into the optical path, and the photographing light amount input unit 36 is operated between F3 and F8 while the set value of the observation light amount input unit 35 is fixed at 8. The process proceeds to steps S1, S7, and S11, and is determined to be the flash photography mode.

  Since the control in step S6 at time T2 is the same as that in the first embodiment, the description thereof is omitted. In the second embodiment, the observation initial data storage unit 32b and the imaging initial data storage unit 32e are set to the values 7 and F3, but it goes without saying that the values differ depending on the configuration of the ophthalmologic apparatus.

  Furthermore, although the setting values of the observation light quantity input unit 35 are 1 to 9 and the photographing light quantity input unit 36 are F1 to F8, they can be set more finely. For the purpose of improving responsiveness, the switches 35a and 35b of the observation light amount input unit 35 and the switches 36a and 36b of the photographing light amount input unit 36 may be dial type switches.

  The preferred embodiments of the present invention have been described above, but the present invention is not limited to these embodiments, and various modifications and changes can be made within the scope of the gist thereof.

It is a block diagram of a fundus camera. It is a block circuit block diagram. It is a graph with respect to the time of the fluorescence luminance of the fundus. It is explanatory drawing of the relationship between the setting value of an observation light quantity input part, and the value of an imaging light quantity input part. It is an operation | movement flowchart figure of a control part. FIG. 10 is a graph of the fundus fluorescence luminance with respect to time in Example 2.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Observation light source 2 Objective lens 4 Imaging light source 7a ICG exciter filter 9 Perforated mirror 10a Visible fluorescent barrier filter 11 Shooting lens 14, 20 Imaging element 18a Barrier filter for ICG imaging 18b Barrier filter for ICG observation 21 Barrier filter detection means 31 Amplification factor changing means 32 Control unit 33 Monitor 34 Memory 35 Observation light quantity input part 36 Shooting light quantity input part 37 Shooting switch 38 Observation light source dimming means 39 Imaging light source dimming means

Claims (5)

  An illumination optical system that includes an observation light source and a photographing light source and illuminates the eye to be examined, an observation optical system that observes the eye to be examined, a photographing optical system that photographs the eye to be examined, the observation optical system, and the photographing optical system An imaging unit provided; an observation light amount input unit that sets an observation light amount by the observation light source; an observation light amount control unit that is connected to the observation light amount input unit and adjusts the light amount of the observation light source; and A photographing light quantity input means for setting a photographing light quantity, a photographing light quantity control means for adjusting the light quantity of the photographing light source connected to the photographing light quantity input means, a non-light emitting photographing operation means for photographing using the observation light source, An ophthalmologic photographing apparatus comprising: a photographing operation switching means for switching a light emitting photographing operation means for photographing using the photographing light source; and the non-light-emitting photographing operation means and the light emitting device by the photographing operation switching means. When performing switching of the photographing operation unit, an ophthalmologic photographing apparatus characterized by performing the initial setting of the light amount control by the observation light amount control unit or the imaging light amount control means.   An amplification factor changing unit is provided for changing an amplification factor of an image captured by the imaging unit, the amplification factor changing unit is changed by the observation light amount input unit and the photographing light amount input unit, and the amplification factor is an initial value of the light amount control. The ophthalmologic photographing apparatus according to claim 1, wherein the ophthalmologic photographing apparatus is included in setting.   The ophthalmologic photographing apparatus according to claim 1, wherein the photographing operation switching unit performs switching according to a state of the observation light amount input unit and a state of the photographing light amount input unit.   The ophthalmologic photographing apparatus according to any one of claims 1 to 3, wherein a fluorescence filter can be inserted into the illumination optical system and the photographing optical system.   5. The optical path length correction glass is inserted instead when the fluorescence filter is not inserted into the illumination optical system and the imaging optical system. 6. Ophthalmic photography device.

Images