JPH0528129B2 - - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION [Industrial Field of Application] The present invention relates to an endoscope imaging device that is capable of selecting an observation wavelength range depending on an object to be observed.

[Prior Art and Problems to be Solved by the Invention] In recent years, various electronic endoscopes using solid-state imaging devices such as charge-coupled devices (CCDs) as imaging means have been proposed.

This electronic endoscope has advantages such as higher resolution than fiberscopes, easier recording and reproduction of images, and easier image processing such as magnification and comparison of two images.

By the way, when observing an object to be observed using an imaging device such as the electronic endoscope, it is necessary to detect (recognize) subtle differences in color tone, especially when distinguishing between affected areas and normal areas in living organisms. be. However, when the change in color tone of the observed area is subtle, detecting this subtle difference requires advanced knowledge and experience, and it takes a long time to detect it, and it takes a long time to detect it. Even if I concentrated my attention, it was difficult to always make appropriate decisions.

To deal with this, for example, Japanese Patent Application Laid-Open No. 56-3033 focuses on the fact that there are cases where the change in color tone becomes large in a region other than the visible region, for example, in the infrared wavelength region. The object to be observed is illuminated by guiding spectroscopic light having a wavelength range in a time-series manner.
A technology has been disclosed that focuses reflected light from an object to be observed on a solid-state imaging device, converts it into an electrical signal, processes the electrical signal according to the wavelength range, and displays an image in the wavelength range using a specific color signal. has been done. According to this conventional example, invisible information obtained in the infrared wavelength region can be converted into visible information, and, for example, it is possible to quickly and easily distinguish between an affected area and a normal area.

However, in the above conventional example, since the observation wavelength range is fixed, for example, when using infrared light, images in the general visible range cannot be obtained.
It is difficult to compare both images, and there are also problems such as there being no effect on objects to be observed that have characteristics in other wavelength regions.

For example, Japanese Patent Application Laid-Open No. 59-139237 discloses that fluorescence generated from a living body in response to excitation light irradiation is passed through multiple types of bandpass filters to take multiple images, and each image has a density level. A technique has been disclosed in which each difference is assigned a different color tone, and each difference is configured into a single pseudo-color image.

However, in this related technology example, although it is possible to identify differences in density, it is not possible to identify differences in tone.

Furthermore, Japanese Patent Application Laid-open No. 181720/1983 discloses that a solid-state imaging device in the tip of an endoscope insertion section and an objective lens are designed to enable imaging and observation using visible light, infrared light, ultraviolet light, etc. An endoscope device is shown in which an imaging-side filter is provided at the end of the image pickup side, and a light source-side filter is provided in front of the white lamp of the light source device. The imaging side filter includes an infrared light transmitting filter, a visible light transmitting filter, and an ultraviolet light transmitting filter, any of which is selected. In addition, the light source side filter is composed of a red filter, a green filter, and a blue filter that transmit red, green, and blue color light, and one of them is selected, and the red filter is not limited to the normal red wavelength range. , it also has the property of transmitting infrared light with longer wavelengths.

However, in the above-mentioned conventional example, it is necessary to arrange the filter device not only on the light source device side but also in the distal end of the endoscope insertion section, which is required to have a smaller diameter, and the structure of the distal end becomes complicated. When the diameter becomes thicker, there are certain disadvantages. Further, the light source side filter,
For example, since a red filter is used for both normal visible light observation and infrared light observation, when observing infrared light, normal red light is transmitted in addition to infrared light, and the subject is irradiated with it. As a result, the temperature of the distal end of the endoscope containing the solid-state imaging device and the living body, which is the subject, increases accordingly.

[Object of the Invention] The present invention has been made in view of these circumstances, and is intended to reduce the diameter of a filter device for obtaining light in the visible light region or a wavelength region other than visible light. It does not need to be placed inside the distal end of the endoscope insertion section, so it can provide illumination in the optimal wavelength range according to the object to be observed, without complicating the configuration inside the end of the endoscope insertion section or increasing the diameter. It is possible to obtain visible information by selecting the light, and it is possible to easily detect color tone differences in each part of the object to be observed, which are difficult to distinguish with images in the general visible range. For endoscopes, only the illumination light in the wavelength range is selected and irradiated, thereby preventing the temperature rise of the endoscope insertion section tip or the object to be observed due to illumination light in the redundant wavelength range. The purpose is to provide an imaging device.

[Means for Solving the Problems] In order to achieve the above object, the endoscope imaging device according to the present invention includes an illumination unit that switches illumination light in the visible light region or at least illumination light in a wavelength region other than the visible light region. and an imaging means that is sensitive to at least a wavelength region other than the visible light region, which images a subject image in the wavelength range illuminated by the illumination means, and a visible color image from the image obtained by the imaging means. means for obtaining an image that includes information in a wavelength range other than the visible light range; and means for selectively displaying at least one of the images; The optimal wavelength range according to the object to be observed is selected and displayed from among the images containing information on the object.

[Example] Hereinafter, an example of the present invention will be described with reference to the drawings.

1 to 6 relate to a first embodiment of the present invention, and FIG. 1 is a block diagram showing the configuration of an imaging device;
Fig. 2 is a side view showing the entire electronic endoscope device, Fig. 3 is an explanatory view showing the band switching filter, Fig. 4 is an explanatory drawing showing the rotary filter, and Fig. 5 is an illustration of each filter of the band switching filter. FIG. 6 is an explanatory diagram showing the transmission wavelength band, and FIG. 6 is an explanatory diagram showing the transmission characteristics of each filter of the rotary filter.

The endoscope imaging device of this embodiment is applied to, for example, an electronic endoscope 1 as shown in FIG. This electronic endoscope 1 has a large-diameter operating section 3 connected to the rear end of an elongated, for example, flexible insertion section 2 . A flexible cable 4 is connected to the side from the rear end of the operating section 3.
is extended, and a connector 5 is provided at the tip of this cable 4. The electronic endoscope 1 is connected via the connector 5 to a control device 6 that includes a light source section and a video signal processing section. Furthermore, a color CRT monitor 7 is connected to the control device 6 as a display means.

On the distal end side of the insertion portion 2, a rigid distal end portion 9 and a bendable portion 10 adjacent to the distal end portion 9 and capable of bending toward the rear side are sequentially provided. Furthermore, by rotating a bending operation knob 11 provided on the operating section 3, the bending section 10 can be bent in the left-right direction or in the up-down direction.
Further, the operating section 3 is provided with an insertion port 12 that communicates with a forceps channel provided in the insertion section 2.

The imaging device 21 of this embodiment is configured as shown in FIG.

A light source section 22 having a light source 24 is provided within the control device 6 . The light source 24 is a light source that emits wavelengths in a wide range from the ultraviolet region to the infrared region, including the visible region, and can be a general halogen lamp, xenon lamp, strobe lamp, or the like. The lighting of this light source 24 is controlled by a light source lighting device 26 that is controlled by a control section 25. In front of the light source 24, a band switching filter 27 as a selection means is rotatably driven by a drive motor 28.
is installed. This band switching filter 27
As shown in FIG. 3, it is divided into three parts in the circumferential direction, and each divided part is provided with a filter 27a, which transmits the ultraviolet band, visible band, and infrared band, as shown in FIG. 27b and 27c are arranged. Therefore, this band switching filter 27 selectively transmits any one of the ultraviolet band, visible band, and infrared band. Note that the drive motor 2
The rotation of the motor 8 is controlled by a motor driver 29 which is controlled by the control section 25.

Further, in front of the light passing through the band switching filter 27 in the traveling direction, there is a rotary filter 31 as a dividing means that is rotationally driven by a drive motor 30.
is installed. As shown in FIG. 4, this rotary filter 31 is divided into nine parts in the circumferential direction. Ultraviolet light (UV1), first infrared light (IR1), green (G), second ultraviolet light (UV2), second infrared light (IR2), blue (B), third ultraviolet light Filters 31a to 31i that transmit light (UV3) and third infrared light (IR3) are arranged in this order. Note that the first to third infrared lights are
The wavelength ranges are different from each other, and the center wavelength becomes longer in the order of IR1, IR2, and IR3. Similarly, the first to third ultraviolet lights have different wavelength ranges,
The center wavelength becomes longer in the order of UV1, UV2, and UV3. The drive motor 30 also includes a motor driver 32 controlled by the control section 25.
The rotation is controlled by

The light transmitted through the rotary filter 31 and emitted from the light source section 22 is transmitted to the cable 4 and the insertion section 2.
The light is incident on the light guide 33 inserted therein, and guided to the tip 9 via this light guide 33.
The light is emitted from the light distribution lens system 34 provided at the tip 9 and illuminates the object to be observed.

In this embodiment, the combination of wavelength regions of the light emitted from the rotary filter 31 is switched according to the band selected by the band switching filter 27. That is, the band switching filter 27
When the infrared band is selected by ,
Green (G) and blue (B) color lights are emitted in time series, and if the ultraviolet band is selected, the first to third ultraviolet lights UV1, UV2, and UV3 are emitted in time series. It is emitted.

On the other hand, at the imaging position of the objective lens system 35 provided at the tip 9, a solid-state image pickup device 36 as an image pickup means is disposed. This solid-state image sensor 3
No. 6 has sensitivity in a wide wavelength range from the ultraviolet region to the infrared region, including the visible region. Moreover, each filter 31a to 31i of the rotary filter 31 is
The solid-state image sensor 36 has a transmission characteristic within a range in which it has sensitivity.

The image of the object to be observed formed on the solid-state image sensor 36 is photoelectrically converted, and signals corresponding to each pixel of the solid-state image sensor 36 are converted by a driver 37 controlled by the control section 25. It is read out in chronological order in synchronization with the switching of illumination light. The output signals of the solid-state image sensor 36 are transmitted to the process circuit 3 controlled by the control section 25.
8, a matrix circuit 39 and an encoder 40 are input to a video signal processing section 41. The output signal of the solid-state image sensor 36 is first sent to the process circuit 38.
is input. In this process circuit 38, each color of red (R), green (G), and blue (B) is arbitrarily assigned to the output signal corresponding to the illumination light in each wavelength range.
R, G, and B color signals are generated.

The R, G, and B color signals from the process circuit 38 are input to a matrix circuit 39, and the matrix circuit 39 converts the R, G, and B color signals into, for example, an NTSC luminance signal Y and a color difference signal R-Y. , B
-Y is generated. Furthermore, the output of this matrix circuit 39 is input to an encoder 40, which generates an NTSC video signal. This video signal is then input to the color CRT monitor 7, so that the object to be observed is displayed in color.

In this embodiment configured as described above, the wavelength range to which the solid-state image sensor 36 is sensitive is divided by the rotating filter 31 into nine wavelength ranges UV1 to IR3. Then, in the band switching filter 27, ultraviolet,
By selecting either the visible or infrared band, 3 out of the 9 wavelength ranges UV1 to IR3 can be selected.
A wavelength range is selected. The combination of these three wavelength regions is the first to third ultraviolet light UV1 to UV3, red (R),
These are green (G) and blue (B) color lights, or first to third infrared lights IR1 to IR3. Then, the light in the selected three wavelength ranges is irradiated onto the object to be observed in a time-series manner.

The reflected light of the object to be observed corresponding to each illumination light in the selected three wavelength regions is photoelectrically converted by the solid-state image sensor 36 and read out in time series in synchronization with the switching of the illumination light.

Then, the output signals corresponding to each illumination light of the solid-state image sensor 36 are arbitrarily assigned each color of red (R), green (G), and blue (B) in a video signal processing section 41, and are converted into video signals. It is processed.

Then, the object to be observed is displayed in color using each assigned color. That is, when the ultraviolet band or the infrared band is selected by the band switching filter 27, the object to be observed is displayed in pseudo color.

In this way, according to this embodiment, ultraviolet, visible,
By selecting an arbitrary infrared band and assigning arbitrary colors, the object to be observed can be displayed in color, and the optimum observation wavelength band can be selected depending on the object to be observed. Therefore, it becomes easy to detect the difference in color tone between each part of the object to be observed, which is difficult to distinguish using images in a general visible range.

Note that the band switching filter 27 is not limited to one that is divided into an ultraviolet region, a visible region, and an infrared region. A filter is provided, and the light transmitted through this filter is sent to a rotating filter 3.
The green (G), red (R) color lights, and the first infrared light (IR1) are irradiated onto the observed object in time series. Color display may be performed by assigning each color of blue (B), green (G), and red (R) to each color light of R) and the first infrared light (IR1). Then, such a color image may be compared with a color image in a general visible range. In this way, various color images can be obtained by combining the band switching filter 27 and the rotary filter 31.

Further, the band switching filter 27 and the rotary filter 31 may be arranged between the light source 24 and the solid-state image sensor 36, and the order of arrangement can be arbitrarily determined.

In addition, each filter 31a of the rotary filter 31
The chronological arrangement of 31i can be appropriately set in relation to the timing of reading from the solid-state image sensor 36.

Furthermore, the light source 24 is not limited to one that emits light in all of the ultraviolet, visible, and infrared regions, but for example, a plurality of light sources that emit light in at least one of these bands may be provided and used by switching. You can also do it.

Further, for example, when a line transfer type CCD is used as the solid-state image sensor 36, when using red (R), green (G), and blue (B) color lights as illumination light, for example, UV1+IR1, UV2+IR2, UV3+
IR3 is used as a light shielding part, and IR1~IR3 is used as illumination light.
When using G+UV2, B+UV3, R+
UV1 may be used as a light shielding part.

In addition, a strobe lamp that can be turned on and off at high speed is used as the light source 24 without using a wavelength band limiting filter such as the band switching filter 27.
The required wavelength bands UV1 to UV3, B, G, R, of each filter 31a to 31i of the rotary filter 31,
By emitting light when the filters IR1 to IR3 are on the optical path, other filter sections may be used as the readout period.

7 and 8 are block diagrams showing an imaging apparatus according to a second embodiment of the present invention.

In this embodiment, a plurality of light sources each emitting light in a different specific wavelength range are provided. A narrow band light source such as a laser is used as the plurality of light sources 45a to 45d. The control unit 25 selects one to three light sources from among the plurality of light sources 45a to 45d.
A number of light sources are selected, and the selected light sources are caused to emit light in chronological order in synchronization with the readout timing of the solid-state image sensor 36. Then, the light of the selected three wavelength regions is irradiated onto the object to be observed in a time-series manner. The other configurations are the same as in the first embodiment.

As a means for making the light selectively emitted from the plurality of light sources 45a to 45d enter one light guide 33, there is, for example, one shown in FIG. That is, one light source 45a is arranged at a position where the light emitted from this light source 45a directly enters the light guide 33, and the light emitted from the other light sources 45b to 45d is
The light is made to enter the light guide 33 via mirrors 46b to 46d and rotatable mirrors 47b to 47d disposed between the light source 45a and the light guide 33. And the light source 45
When the light emitted from a is made to enter the light guide 33, all of the mirrors 47b to 47d are retreated from the illumination optical path of the light source 45a. Further, when the light emitted from the other light sources 45b to 45d is made to enter the light guide 33, the mirror 4
Among the mirrors 7b to 47d, only the mirror corresponding to the light source that emits light is interposed in the illumination optical path of the light source 45a.

Further, as another means for making the light selectively emitted from the plurality of light sources 45a to 45d enter one light guide 33, for example, as shown in FIG. The light guide 33 may be movable, and the light source emitting light may be selectively opposed to the incident end of the light guide 33.

Note that the light sources 45a to 4 shown in FIG. 7 or 8
Lamps used for 5d include lasers and LEDs that emit light with a limited wavelength.
Further, an absorption type filter or a vapor deposition type filter containing a dye may be provided at the exit of a lamp such as a xenon lamp, a halogen lamp, or a strobe lamp that emits broadband light to limit the output wavelength.

According to this embodiment, the wavelength range can be selected more freely.

9 to 11 relate to the third embodiment of the present invention, FIG. 9 is a block diagram showing an imaging device, and FIG.
FIG. 0 is an explanatory diagram showing a rotary filter, and FIG. 11 is a timing chart for explaining the operation of this embodiment.

In this embodiment, a color filter 50 as shown in FIG. 10 is disposed in front of the light source 24.
Similar to the rotary filter 31 in the first embodiment, this color filter 50 is divided into nine parts in the circumferential direction, and each divided part has a red color (R) having a transmission characteristic as shown in FIG. ), first ultraviolet light (UV1), first infrared light (IR1), green (G), second ultraviolet light (UV2), second infrared light (IR2), blue (B), Filters 50a to 50i that transmit third ultraviolet light (UV3) and third infrared light (IR3) are arranged in this order. Further, each of the filters 50a to 50i
A light shielding portion 51 is provided between them.

The light in each wavelength range that has passed through each of the filters 50a to 50i is irradiated onto the object in time series. When the wavelength range of this illumination light is switched, a light-shielding period corresponding to the light-shielding portion 51 is provided. In this embodiment, signals from the solid-state image sensor 36 are read out during this light-blocking period.

Further, in this embodiment, a selection circuit 52 is provided between the solid-state image sensor 36 and the video signal processing section 41. This selection circuit 52 is controlled by the control section 25 and is configured to select the output signal of the solid-state image sensor 36 at a predetermined timing and send it to the video signal processing section 41.

The selection timing of this selection circuit 52 is
Shown in Figures a to 11e. That is, when performing observation in the visible band, the signals at the time of readout corresponding to the R, G, and B illumination lights are When observing in the ultraviolet band, as shown in Figure 11c, UV1, UV2,
When selecting a signal during readout corresponding to UV3 illumination light and performing observation in the infrared band, the first
As shown in Figure 1d, signals are selected during readout corresponding to the illumination lights of IR1, IR2, and IR3. In addition, when observing in some bands of the long wavelength side of the visible region and the short wavelength side of the infrared region, readout corresponding to the R, IR1, and G illumination lights is performed as shown in Figure 11e. Select the signal at the time.

According to this embodiment, as in the second embodiment, the wavelength range can be selected more freely.

In the first to third embodiments described above, the object to be observed may be irradiated with illumination light and the light transmitted through the object to be observed may be received. In addition, the imaging means is not limited to a solid-state imaging device installed at the tip of the endoscope, but can also be an external television camera attached to the eyepiece of the endoscope that transmits the observation image using an image guide. It's okay.

12 to 15 relate to a fourth embodiment of the present invention, and FIG. 12 is a block diagram showing an imaging device;
FIG. 13 is an explanatory diagram showing a rotary filter, FIG. 14 is a timing chart for explaining the operation of this embodiment, and FIG. 15 is an explanatory diagram showing changes in spectral characteristics of blood due to ICG contamination.

In this embodiment, the observation wavelength band can be switched by using a strobe lamp 24S as the light source 24 instead of the band switching filter 27, motor 28, and motor driver 29 in the first embodiment. be. In addition, in this example,
In place of the rotary filter 31 in the first embodiment, a rotary filter 55 having a different arrangement of filters from the rotary filter 31 is provided. As shown in FIG. 13, this rotary filter 55 is divided into nine parts in the circumferential direction, and each divided part has R,
Filters 55a to 55i that transmit G, B, IR1, IR2, IR3, UV1, UV2, and UV3 are arranged in this order. Further, a light shielding portion 56 is provided between each of the filters 55a to 55i.

When the rotary filter 55 is rotated, the fourteenth
As shown in FIG. a, the filters 55a to 55i of the rotary filter 55 are arranged on the illumination optical path of the strobe lamp 24S in chronological order. The strobe lamp 24S can emit light for a short time, and emits light when a filter corresponding to a wavelength range selected by the control section 25 comes on the optical path. Then, a subject image corresponding to the light emitted from the strobe lamp 24S and transmitted through the selected filter is captured by the solid-state image sensor 36.

The other configurations are the same as in the first embodiment.

In this embodiment, for example, as shown in FIG. 14b, filters 5 corresponding to R, G, and B wavelength regions are used.
5a, 55b, 55c are on the optical path, the strobe lamp 24S is made to emit light, and the R, G, B
By applying each of the R, G, and B colors to the wavelength range of , a color image in the normal visible range can be obtained.

Also, as shown in Figure 14c, IR1, IR2,
Filters 55d, 55 corresponding to the IR3 wavelength range
By causing the strobe lamp 24S to emit light when the light beams e and 55f come on the optical path, the subject image in the infrared region is displayed in pseudo color. Similarly, as shown in FIG. 14d, filters 55g, 55h, 55 corresponding to the UV1, UV2, and UV3 wavelength regions
By causing the strobe lamp 24S to emit light when i comes on the optical path, the subject image in the ultraviolet region is displayed in pseudo color.

By the way, FIG. 15 shows changes in the spectral characteristics of blood when indocyanine green (ICG), an infrared absorbing dye, is mixed. As shown in this figure, ICG-laced blood has a maximum absorption at 805 nm. Therefore, filter 55e corresponding to IR2
is a bandpass characteristic centered on 805nm, where the absorption rate is maximum, and a filter 55f corresponding to IR3 is used.
850n, where almost no change in absorption rate is observed.
It has a characteristic of transmitting a wavelength range of m or more. Then, the ICG is mixed into the blood, for example, by intravenous injection, and as shown in FIG.
When f and 55b come on the optical path, the strobe lamp 24S is emitted and the subject is displayed in pseudo color using a combination of the wavelength ranges of IR2, IR3 and G. You can check the running status of the vehicle. That is,
By using infrared light, which has good tissue penetration, it is possible for the light to reach deep into the tissue, while blood has maximum absorption at 805 nm due to the action of ICG, so the ability to reach the tissue is reduced. are similar
Of IR2 and IR3, IR2 is absorbed more, and in an image based on IR2, a shadow appears in the blood vessel area. Therefore, by taking the difference from the IR3 image, it is possible to visualize the running state of blood vessels with good contrast. In addition, the G-based image makes it possible to clearly confirm the unevenness of the surface of the mucous membrane and the state of hyperemia, thereby improving diagnostic ability.

Alternatively, as shown in FIG. 14f, the strobe lamp 24S may be emitted when the subject comes on the filter optical path corresponding to a specific single wavelength range, and the subject image in this wavelength range may be displayed in monochrome. .
In Fig. 14f, only the image of B is obtained, but the absorption characteristics of hemoglobin by R, IR1, IR2, and IR3 on the long wavelength side are greater in the short wavelength region of B. , it becomes possible to clearly observe the distribution of hemoglobin on the mucosal surface. It is also possible to use other single wavelength regions and diagnose lesions etc. from the differences in depiction between the wavelength regions.

Furthermore, by configuring the rotary filter 55 with a filter arrangement as shown in FIG.
When performing normal color display using G and B, R,
Filters 55a, 5 corresponding to the G and B wavelength regions
Since 5b and 55c are close to each other, there is an effect that color shift can be reduced.

16 to 18 relate to a fifth embodiment of the present invention, in which FIG. 16 is an explanatory diagram showing the configuration of an endoscope device, FIG. 17 is an explanatory diagram showing a rotary filter, and FIG.
FIG. 8 is a timing chart for explaining the operation of this embodiment.

This embodiment is an example of an endoscope apparatus in which an external television camera is attached to the eyepiece of a fiberscope.

As shown in FIG.
includes an elongated, for example, flexible insertion section 62, and a large-diameter operation section 63 is connected to the rear end of the insertion section 62. A flexible light guide cable 64 extends laterally from the rear end of the operating section 63. Further, an eyepiece section 65 is provided at the rear end of the operation section 63.

A light guide 69 is inserted into the insertion portion 62 , and a distal end surface of the light guide 69 is disposed at the distal end portion 66 of the insertion portion 62 .
It is designed to be able to emit illumination light from. The incident end side of the light guide 69 is inserted into the light guide cable 64 and connected to a connector (not shown) provided at the tip of the light guide cable 64, and is connected to the control device 6 through this connector. The light emitted from the strobe lamp 24S in the control device 6 is connected to the control device 6.

Further, an objective lens system 67 is provided at the distal end portion 66.
is provided, and the front end surface of an image guide 68 is arranged at the imaging position of this objective lens system 67. This image guide 68 is connected to the insertion section 62.
It is inserted into the eyepiece and extends to the eyepiece section 65. The object image formed by the objective lens system 67 is guided to the eyepiece 65 by the image guide 68 and is observed from the eyepiece 65.

Further, an external television camera 70 is detachably attached to the eyepiece section 65. This external television camera 70 includes an imaging lens 71 that forms an image of the light from the eyepiece 65, and a solid-state image sensor 72 disposed at the imaging position of this imaging lens 71. This solid-state image sensor 72
is driven by the driver 37 in the control device 6, and the read signal is as in the fourth embodiment.
Signal processing is performed by the video signal processing section 41.

The rest of the configuration is substantially the same as that of the fourth embodiment, but a rotary filter 58 is provided in place of the rotary filter 55 in the fourth embodiment. As shown in FIG. 17, this rotary filter 58 is divided into 10 parts in the circumferential direction, and each divided part has R, G, B, IR1, IR2, IR3, UV1, UV2,
Filter 58a~ that transmits UV3, W (white light)
58j are arranged in this order. The filter 58j that transmits W is provided to enable observation using general visible light from the eyepiece 65 of the fiberscope 60, and transmits almost all of the light emitted by the strobe lamp 24S. It may be a filter that transmits only visible light. Furthermore, a light shielding portion 59 is provided between each of the filters 58a to 58j.

When the rotary filter 58 is rotated, the 18th
As shown in Figure a, each of the filters 58a to 58j of the rotary filter 55 is interposed on the illumination optical path of the strobe lamp 24S in chronological order. The strobe lamp 24S emits light when a filter corresponding to a wavelength range selected by the control unit 25 comes on the optical path. The light emitted from the strobe lamp 24S and transmitted through the selected filter is incident on the incident end of the light guide 69 of the fiberscope 60, and the light is transmitted through the selected filter.
It is emitted from 6. The return light from the object caused by this illumination light is imaged by the objective lens system 67 on the tip surface of the image guide 68, and this object image is guided to the eyepiece section 65 by the image guide 68, and further, An image is taken by a solid-state image sensor 72 in an external television camera 70 connected to this eyepiece 65.

In this embodiment, as in the fourth embodiment, as shown in FIG. 24S and emit light in the R, G, and B wavelength regions, respectively.
By assigning colors to each color, a color image in the normal visible range can be obtained.

Also, as shown in Figure 18c, IR1, IR2,
Filters 58d, 58 corresponding to the IR3 wavelength range
When e, 58f comes on the optical path, strobe lamp 2
By emitting light from the 4S, a subject image in the infrared region is displayed in pseudo color. Similarly, the first
As shown in Figure 8d, filters 58g, 58h, 58i corresponding to the wavelength ranges of UV1, UV2, and UV3
By causing the strobe lamp 24S to emit light when the object is on the optical path, the object image in the ultraviolet region is displayed in pseudo color.

Further, as in the fourth embodiment, the filter 58e corresponding to IR2 has a bandpass characteristic centered on 805 nm, and the filter 58f corresponding to IR3 has a bandpass characteristic centered on 805 nm.
It has the characteristic of transmitting wavelength range of 850nm or more,
The ICG is mixed into the blood, and as shown in FIG. 18e, when the filters 58e, 58f, and 58b corresponding to the wavelength regions of IR2, IR3, and G come on the optical path, the strobe lamp 24S is caused to emit light; Said
When a subject is displayed in pseudo color using a combination of the IR2, IR3, and G wavelength regions, the running state of the submucosal blood vessels can be confirmed from the difference in the outputs of IR2 and IR3. In addition, the G-based image makes it possible to clearly confirm the unevenness of the surface of the mucous membrane and the state of hyperemia, thereby improving diagnostic ability.

Alternatively, as shown in FIG. 18f, the strobe lamp 24S may be emitted when the subject comes on the filter optical path corresponding to a specific single wavelength range, and the subject image in this wavelength range may be displayed in monochrome. .

Furthermore, by stopping the rotary filter 58 at a position where the filter 58j that transmits W is interposed on the optical path, light in the visible light range is constantly emitted, so that the illumination light in the visible light range Accordingly, observation with the naked eye can be performed from the eyepiece section 65 of the fiberscope 60.

As described above, according to this embodiment, not only the electronic endoscope 1 as shown in the first to fourth embodiments, but also
Even with the commonly used fiberscope 60, it is possible to select and observe any wavelength range in the wavelength range including those other than the visible light range.

Other functions and effects are similar to those of the fourth embodiment.

19 to 21 relate to a sixth embodiment of the present invention, in which FIG. 19 is an explanatory diagram showing the configuration of an imaging device, FIG. 20 is a front view of a band switching mirror, and FIG.
The figure is an explanatory diagram showing the reflection characteristics of each mirror of the band switching mirror.

In this embodiment, a reflecting mirror is used as the selection means in place of the band switching filter 27 in the first embodiment.

As shown in FIG. 19, a band switching device 30 is provided within the light source section 22. As shown in FIG. 20, this band switching device 80 has a frame 81d.
It is provided with a band switching mirror 81 having three mirrors 81a, 81b, and 81c arranged in a row and each having a different reflection characteristic. The band switching mirror 81 is disposed so as to reflect the light emitted from the light source 24 at a predetermined angle, and also includes mirrors 81a, 81b,
Arrangement direction of 81c (direction shown by arrow in the figure)
The light emitted from the light source 24 is selectively reflected by one of the mirrors 81a, 81b, and 81c.

The reflection characteristics of the mirrors 81a, 81b, and 81c are as shown in FIG. 21, for example.
That is, the mirror 81a reflects only substantially ultraviolet light, the mirror 81b reflects only substantially visible light, and the mirror 81c reflects only substantially infrared light.

Further, as shown in FIG. 20, a rack 82 is provided on the frame 81d of the band switching mirror 81 along the moving direction. A pinion gear 84 rotated by a motor 83 is engaged with the rack 82. The motor 83 is rotated by a motor driver 86 controlled by a band switching control section 85. By rotating the pinion gear 84, the band switching mirror 81 is moved.

Further, the band switching mirror 81 has three types of opening windows 87a, 87b, and 87c having different opening areas along the movement direction of the mirror 8.
They are provided at intervals equal to the intervals of 1a, 81b, and 81c. Further, the band switching mirror 8
1 and the opening windows 87a, 87b, 87
A light emitting element 88 is located at a position selectively facing c.
A light receiving sensor 89 is provided, and the output of this light receiving sensor 89 is transmitted to the band switching control section 85.
is now being entered. The opening window 87a is provided at a position facing the light emitting element 88 and the light receiving sensor 89 with the mirror 81a interposed on the illumination optical path, and the opening window 87b is provided in a position facing the light emitting element 88 and the light receiving sensor 89 with the mirror 81a interposed on the illumination optical path. The opening window 87c is provided at a position facing the light emitting element 88 and the light receiving sensor 89 when the mirror 81c is installed on the illumination optical path. located at the location. Further, the band control section 85 can identify which of the mirrors 81a, 81b, and 81c is interposed on the illumination optical path based on the difference in the amount of light received by the light receiving sensor 89.

Further, the light reflected by any one of the mirrors 81a, 81b, and 81c is reflected by a mirror 90 that reflects light in all bands from ultraviolet to infrared, and the light reflected by this mirror 90 is The light is made incident on a rotary filter 31.

The other configurations are the same as in the first embodiment.

In this embodiment, the band switching control section 85
When one of the ultraviolet, visible, and infrared observation bands is selected, the motor 8 is activated via the motor driver 86.
3 is rotated, and the rack 82 and pinion gear 84
As a result, the band switching mirror 81 moves in the direction of the arrow in the figure. Then, when one of the mirrors 81a, 81b, and 81c corresponding to the selected band is interposed on the illumination optical path, one of the aperture windows 87a, 87b, and 87c corresponding to this mirror is connected to the light emitting element 88 and Light emitted from the light emitting element 88 located between the light receiving sensors 89 passes through the opening window and is received by the light receiving sensor 89 . When the amount of light received by the light receiving sensor 89 matches the amount of light preset by the area of the aperture corresponding to the selected band, the band controller 85 stops the rotation of the motor 83. , the band switching mirror 81 is stopped. In this way,
A mirror that reflects only light in a selected band is interposed on the illumination light path. This mirror 81a, 81
The light reflected by mirrors 90 and 81c
After being reflected by the rotary filter 31 and transmitted through the rotating filter 31, the light enters the incident end of the light guide 33.

For example, if you select the visible band, the 19th
As shown in the figure, a mirror 8 that reflects only visible light
1b is interposed on the illumination optical path, and the light emitted from the light source 24 is reflected by the mirror 81b to become visible light, and further transmitted through the rotating filter 31 to be converted into each of R, G, and B. The light is divided into wavelength bands in chronological order. Further, when the ultraviolet band is selected, a mirror 81a that reflects only ultraviolet light is interposed on the illumination optical path, and the light emitted from the light source 24 is
It is reflected by the mirror 81a and turned into ultraviolet light, and further,
By passing through the rotating filter 31,
The light is divided chronologically into each wavelength band of UV1, UV2, and UV3. Furthermore, when the infrared band is selected, a mirror 81c that reflects only infrared light is interposed on the illumination optical path, and the light emitted from the light source 24 is
It is reflected by the mirror 81c and turned into infrared light, and further,
By passing through the rotating filter 31,
The light is divided into IR1, IR2, and IR3 wavelength bands in time series.

Other functions and effects are similar to those of the first embodiment.

Note that the mirrors 81a, 81b, and 81c are not limited to those that are divided into ultraviolet, visible, and infrared regions;
A material having arbitrary spectral characteristics may be used.

22 and 23 relate to a modification of the sixth embodiment, and FIG. 22 is an explanatory diagram showing a modification of the light source section,
FIG. 23 is a front view of the band switching mirror.

In this modification, instead of the band switching mirror 81 in the sixth embodiment, a rotating mirror 91 that can switch the observation band by rotating is provided.

As shown in FIG. 23, the rotating mirror 91 has a disk-shaped frame 91d divided into three parts in the circumferential direction, and each divided part includes a mirror 91a that reflects only ultraviolet light, a mirror 91a that reflects only ultraviolet light, and a mirror 91a that reflects only ultraviolet light, A mirror 91b that reflects only light and a mirror 91c that reflects only infrared light are provided. This rotating mirror 91 is rotationally driven by a motor 92.
is rotated by a motor driver 93 controlled by a band switching control section 85. Further, as shown in FIG. 23, the rotating mirror 91 includes mirrors 91a, 91
Corresponding to windows b and 91c, three types of opening windows 94a, 94b, and 94c each have different opening areas,
It is provided along the rotation direction. And the sixth
Similar to the embodiment, the opening windows 94a, 94b, and 94c are selectively located between the light emitting element 88 and the light receiving sensor 89, which are disposed with the rotating mirror 91 in between. sensor 8
Depending on the amount of light received by the mirrors 91a, 91
It is possible to identify which one of the lights b and 91c is interposed on the illumination optical path.

Other configurations, operations, and effects are the same as those of the sixth embodiment.

FIGS. 24 and 25 relate to a seventh embodiment of the present invention, in which FIG. 24 is an explanatory diagram showing a light source section, and FIG. 25 is an explanatory diagram showing a rotating filter.

In this embodiment, a rotating mirror 95 is provided in place of the rotating filter 31 in the sixth embodiment.

As shown in FIG. 25, the rotating mirror 95 has a disc-shaped frame divided into nine parts in the circumferential direction, and each divided part has R, G, B,
Mirrors 95a to 95i that reflect only IR1, IR2, IR3, UV1, UV2, and UV3 are arranged in this order. Moreover, between each mirror 95a to 95i,
A light shielding portion 96 is provided that does not reflect light in any band. The rotating mirror 95 is driven by a motor 9.
The motor 97 is rotated by a motor driver 98 that is controlled by the control section 25 .

The rotating mirror 95 is arranged so that the light reflected by the band switching mirror 81 is reflected by one of the mirrors 95a to 95i, and the reflected light is incident on the incident end of the light guide 33. has been done.

The other configurations are the same as those of the sixth embodiment.

In this embodiment, the band switching mirror 81 allows
One of ultraviolet, visible, and ultraviolet observation bands is selected, and the rotating mirror 95 divides the light into wavelength bands of R, G, B, etc. in time series.

Other functions and effects are similar to those of the sixth embodiment.

In this embodiment, instead of the band switching mirror 81, the rotating mirror 91 in the modification of the sixth embodiment may be used, or the band switching filter 27 in the first embodiment may be used.

26 to 30 relate to the eighth embodiment of the present invention, and FIG. 26 is a block diagram showing an imaging device;
FIG. 27 is an explanatory diagram showing the band limiting filter,
FIG. 8 is an explanatory diagram showing the transmission characteristics of each filter of the band limiting filter, FIG. 29 is an explanatory diagram showing the rotary filter, and FIG. 30 is an explanatory diagram showing the transmission characteristic of each filter of the rotary filter.

In this embodiment, the light source 24 emits light ranging from the visible light range to the infrared light range. Furthermore, a band limiting filter 227 as band limiting means is provided in place of the band switching filter 27 in the first embodiment, and a rotating filter 231 is provided in place of the rotating filter 31.

The band limiting filter 227 is divided into two parts in the circumferential direction as shown in FIG. A filter 227b that transmits the outer band is arranged.
Therefore, depending on the position of the band-limiting filter 227, either the visible band or the infrared band of the light emitted from the light source 24 is selectively transmitted.

On the other hand, as shown in FIG. 29, the rotary filter 231 is divided into three parts in the circumferential direction, and each divided part has a filter 231a,
231b and 231c are arranged. In this embodiment, each of the filters 231a, 231b, 23
1c has a double transmission characteristic, and as shown in FIG. 30, the filter 231a transmits R in the visible band and IR in the infrared band, and the filter 231b transmits
Transmits G in the visible band and IR in the infrared band,
The filter 231c is configured to transmit B in the visible band and IR in the infrared band.

The other configurations are the same as in the first embodiment.

In this embodiment, the transmission wavelength range of each filter 231a, 231b, 231c of the rotary filter 231 is determined by the band limiting filter 227.
It is limited to wavelengths that belong to either the visible band or the infrared band. That is, when the visible band is selected by the band limiting filter 227, only visible light enters the rotating filter 231, so the rotating filter 231 selects R, G, and B.
The light is color-separated in chronological order and sent to the light guide 3.
It enters the input end of No. 3. On the other hand, when the infrared band is selected by the band-limiting filter 227, only infrared light enters the rotary filter 231.
Without performing B color separation, light in the infrared band IR is emitted from this rotary filter 231 and enters the input end of the light guide 33.

When the visible band is selected by the band-limiting filter 227, the object to be observed is irradiated with light in each of the R, G, and B wavelength regions in time series, and the returned light from the object to be observed is By the objective lens system 35,
The image is formed on the solid-state image sensor 36. This solid-state image sensor 36 is driven by a driver 37, and the signals read out from the solid-state image sensor 36 corresponding to each wavelength region are sent to a video signal processing unit 41, where they are arbitrarily processed into red, green, and blue colors. is assigned and the video signal is processed. For example, the output signal of the solid-state image sensor 36 is subjected to signal processing such as amplification and γ correction in a process circuit 38, and the color signal is corrected in a matrix circuit 39 so as to provide colorimetrically accurate color reproduction. Furthermore, the encoder 40 temporarily stores three types of images color-separated into each wavelength range, and converts them into a video signal that can be viewed on a general television monitor.
It is output to the monitor 7. Therefore, when red, green, and blue colors are assigned to each of the R, G, and B wavelength regions, a normal color image is obtained.

On the other hand, when the infrared band is selected by the band limiting filter 227, the object to be observed is in the infrared band regardless of the position of the rotary filter 231.
IR light is irradiated, and the image of the object to be observed in the infrared band is displayed in monochrome.

As described above, according to this embodiment, it is possible to switch between a color image in the visible region and an image in the infrared region, and it is possible to detect submucosal lesions and blood vessels that are difficult to detect using only visible light. It becomes possible to check the condition and improve diagnostic ability.

Note that each filter 23 of the rotary filter 231
1a, 231b, and 231c are not limited to those that transmit R, G, and B, respectively, in the visible band, as shown in FIG. 30; for example, as shown in FIG. 31, they each transmit yellow ( Ye),
It may be one that transmits green (G) and cyan (Cy).

Further, the band limiting filter 227 has a 27th
As shown in the figure, the frame body 228 is not limited to a disk shape, but for example, as shown in FIG.
By arranging a filter 228a that transmits the visible band and a filter 228b that transmits the infrared band along the circumferential direction, and rotating the frame 228 by a predetermined angle around the rotation axis 229, the filter 2
One of 28a and 228b may be selectively interposed on the illumination optical path of the light source 24. Further, as shown in FIG. 33, the frame body 231
Filters 231a that transmit the visible band are placed on the left and right sides of the
and a filter 231b that transmits an infrared band.For example, the frame body 2
By moving the filter 31 in the left-right direction, one of the filters 231a and 231b may be selectively interposed on the illumination optical path of the light source 24.

34 to 36 relate to the ninth embodiment of the present invention, FIG. 34 is an explanatory diagram showing the light source section, and FIG. 35 is an explanatory diagram showing the light source section.
FIG. 36 is an explanatory diagram showing the transmission characteristics of a narrowband band-limiting filter, and FIG. 36 is an explanatory diagram showing the difference in spectral characteristics between blood mixed with ICG and blood not mixed with ICG.

In this embodiment, a band-limiting filter 240 is provided in the light source section 22 in the eighth embodiment so as to be freely insertable and removable in the illumination optical path of the light source 24. As shown in FIG. 35, the band limiting filter 240 has a narrow band pass characteristic centered at 805 nm. Note that the transmission wavelength band W0 of this band-limiting filter 240 is as narrow as possible.
The thickness is preferably about 40 nm or less.

The other configurations are the same as those of the eighth embodiment.

Figure 36 is an ultraviolet absorbing dye.
Blood contaminated with Indocyanine green (ICG) and ICG
It shows the difference in spectral characteristics (attenuation rate due to ICG contamination) with blood without contamination. As shown in this figure,
Blood mixed with ICG has maximum absorption at 805 nm. Therefore, for example, ICG can be administered into the blood by intravenous injection.
When the band-limiting filter 227 selects the infrared band, and the band-limiting filter 240 having a bandpass characteristic centered on 805 nm where the absorption rate is maximum is interposed in the illumination optical path of the light source 24, The object to be observed is irradiated with a narrow band of light centered around 805 nm, and an image of the object in this narrow band is observed. Light centered at 805 nm reaches deep into the mucous membrane and is absorbed in the blood vessels, so the blood vessels are observed as shadows. Therefore, the running state of blood vessels can be observed with much better contrast than when observing in other wavelength ranges.

Note that the band-limiting filter 240 is connected to the light source 24.
The effect when evacuated from the illumination optical path is the same as in the eighth embodiment. Furthermore, it goes without saying that the rotary filter 231 may be one having the transmission characteristics shown in FIG. 31.

Incidentally, instead of inserting the band-limiting filter 240 into the illumination optical path, as shown in FIG.
A light source 241 such as a laser or LED that emits light in a narrow band centered on 805 nm is prepared, and when observing an object image in a narrow band centered on 805 nm, the light source 24 that emits light in a wide band is prepared. Alternatively, the light source 241 may be used.

FIG. 38 is an explanatory diagram showing the transmission characteristics of each filter of the rotary filter in the tenth embodiment of the present invention.

In this embodiment, each filter 231a, 231b, 231 of the rotary filter 231 in the eighth embodiment
As shown in FIG. 38, the filter 231a transmits R in the visible band and a narrow band centered at 805 nm, and the filter 231b
The filter 231c transmits G in the visible band and a narrow band centered at 805 nm, and the filter 231c transmits B in the visible band and a narrow band centered at 805 nm.

The other configurations are the same as those of the eighth embodiment.

In this embodiment, when the band-limiting filter 227 selects the visible band, a color image in the normal visible band is obtained; on the other hand, when the band-limiting filter 227 selects the infrared band, the 805n
Only a narrow band of light centered at m passes through the rotary filter 231, this light is irradiated onto the object to be observed, and an image of the object in this narrow band is observed.

Note that the filters that transmit a narrow band centered on 805 nm are filters 231a, 231b, and 231.
For example, one filter may have the above-mentioned narrow band transmission characteristic.
In this case, at a position where a filter that also transmits this narrow band is inserted in the illumination optical path, the rotary filter 231
By stopping the optical system and selecting the visible band with the band-limiting filter 227, it is possible to observe the image of the object in a narrow band centered at 805 nm. In this way, even if only one filter has the above-mentioned narrow band transmission characteristic, when imaging is performed using the frame sequential method,
There is no reduction in resolution.

39 and 40 relate to the eleventh embodiment of the present invention, FIG. 39 is an explanatory diagram showing a rotary filter, and FIG. 40 is an explanatory diagram showing transmission characteristics of each filter of the rotary filter.

In this embodiment, a rotary filter 251 is provided in place of the rotary filter 231 in the eighth embodiment.

As shown in FIG. 39, the rotating filter 251 is divided into three parts in the circumferential direction, and each divided part has a filter 251a, 251, respectively.
b, 251c are arranged. Each filter 25
1a, 251b, 251c have double transmission characteristics, and as shown in FIG.
is R in the visible band and IR3 in the infrared band.
The filter 231b transmits G in the visible band and IR2 in the infrared band, and the filter 231c transmits B in the visible band and IR1 in the ultraviolet band.

The other configurations are the same as those of the eighth embodiment.

In this embodiment, when the visible band is selected by the band-limiting filter 227, the rotating filter 251 color-separates the R, G, and B lights in time series, as in the eighth embodiment. , a color image in the normal visible range is obtained. On the other hand, when the ultraviolet band is selected by the band limiting filter 227,
IR1, IR2, IR3 by the rotary filter 251
The light is color-separated in time series, and the object to be observed is irradiated with this light. Then, in the video signal processing section 41,
Red, green, and blue colors are arbitrarily assigned to the wavelength regions of IR1, IR2, and IR3, respectively, and the video signal is processed. Therefore, the image of the object to be observed in the ultraviolet band is displayed in pseudo color.

According to this embodiment, the image of the object to be observed can be displayed in color not only in the visible band but also in the infrared band, so it becomes easy to detect the difference in color tone of each part of the object in the infrared band.

41 to 44 relate to the twelfth embodiment of the present invention, in which FIG. 41 is an explanatory diagram showing a band-limiting filter, FIG. 42 is an explanatory diagram showing the transmission characteristics of each filter of the band-limiting filter, and FIG. FIG. 44 is an explanatory diagram showing a rotary filter, and FIG. 44 is an explanatory diagram showing transmission characteristics of each filter of the rotary filter.

In this embodiment, the light source 24 emits light ranging from the visible light range to the ultraviolet light range. Furthermore, the band limiting filter 227 in the eighth embodiment
A band limiting filter 261 is provided instead of , and a rotating filter 262 is provided instead of the rotating filter 231 .

The band limiting filter 261 is divided into two parts in the circumferential direction as shown in FIG. A filter 261b that transmits the band is arranged.
Therefore, depending on the position of the band-limiting filter 261, either the visible band or the ultraviolet band of the light emitted from the light source 24 is selectively transmitted.

On the other hand, as shown in FIG. 43, the rotary filter 262 is divided into three parts in the circumferential direction, and each divided part has a filter 262a,
262b and 262c are arranged. In this embodiment, each of the filters 262a, 262b, 26
As shown in FIG. 44, the filter 262a transmits R in the visible band and UV3 in the ultraviolet band.
The filter 62b is configured to transmit G in the visible band and UV2 in the ultraviolet band, and the filter 262c is configured to transmit B in the visible band and UV1 in the infrared band.

The other configurations are the same as those of the eighth embodiment.

In this embodiment, when the visible band is selected by the band limiting filter 261, the rotary filter 262 selects the R, G, and B bands as in the eighth embodiment.
The light is color-separated in time series to obtain a color image in the normal visible range. On the other hand, when the ultraviolet band is selected by the band limiting filter 261, the rotating filter 262 selects UV1,
UV2 and UV3 light is separated in color in time series, and this light is irradiated onto the object to be observed. Then, in the video signal processing section 41, each color of red, green, and blue is arbitrarily assigned to the UV1, UV2, and UV3 wavelength regions, respectively, and the video signal is processed. Therefore, the image of the object to be observed in the ultraviolet band is displayed in pseudo color.

According to this embodiment, the image of the object to be observed can be displayed in color not only in the visible band but also in the ultraviolet band, making it easy to detect the difference in color tone of each part of the object in the ultraviolet band.

FIG. 45 is an explanatory diagram showing the configuration of an endoscope apparatus according to a seventeenth embodiment of the present invention.

In this embodiment, the imaging device of the eighth embodiment is applied to an external television camera attached to the eyepiece of a fiberscope.

The fiberscope 60 has the same configuration as that shown in the fifth embodiment, so a description thereof will be omitted.

The eyepiece section 65 of the fiberscope 60 includes:
An external TV camera 270 is detachably attached. This external TV camera 2
70 includes an imaging lens 271 on which the light from the eyepiece 65 forms an image, and a solid-state image sensor 272 disposed at the imaging position of the imaging lens 271. Further, the light emitted from the light source 24 passes through a band limiting filter 227 and a rotary filter 231 and is made incident on the incident end of the light guide 69 of the fiberscope 60.

Other configurations, operations, and effects are similar to those of the eighth embodiment.

In this embodiment, the combination of the rotary filter and the band-limiting filter is not limited to the one shown in the eighth embodiment, but may be the combination shown in the ninth to twelfth embodiments.

In the eighth to thirteenth embodiments, a band-limiting filter that can selectively transmit three or more bands such as an ultraviolet band, a visible band, and an infrared band is used, and each of the color filters includes: By using a filter having transmission characteristics in three or more regions selectable by the band-limiting filter, any observation wavelength band can be selected from among the three or more observation wavelength bands. good.

In addition, the observation wavelength bands that can be selected are not limited to those that are resolved into ultraviolet, visible, and infrared. You can set it as you like.

In addition, a band limiting filter, a rotating filter 37
may be arranged between the light source 24 and an imaging means such as the solid-state imaging device 36, and the arrangement order can be determined arbitrarily.

Furthermore, the device is not limited to one that receives reflected light from the object to be observed, but may be one that receives light that has passed through the object to be observed.

Furthermore, the device is not limited to one that receives reflected light from the object to be observed, but may be one that receives light that has passed through the object to be observed.

46 to 51 relate to the fourteenth embodiment of the present invention, in which FIG. 46 is a block diagram showing the configuration of the imaging device, FIG. 47 is an explanatory diagram showing the light emission characteristics of the light source,
FIG. 48 is an explanatory diagram showing a band limiting filter,
FIG. 9 is an explanatory diagram showing the transmission characteristics of each filter of the band limiting filter, FIG. 50 is an explanatory diagram showing the color filter, and FIG. 51 is an explanatory diagram showing the transmission characteristic of each filter of the color filter.

The imaging device of this embodiment is configured as shown in FIG. 46.

A light source 24 is provided within the control device 6 .
As shown in FIG. 47, this light source 24 is a light source that emits light in a wide band of wavelengths ranging from at least the visible region to the infrared region, and can be a general halogen lamp, xenon lamp, or the like. The lighting of this light source 24 is controlled by a light source lighting device 26 that is controlled by a control section 25. In front of the light source 24, a band-limiting filter 328 as a band-limiting means rotationally driven by a drive motor 327 is disposed. This band limiting filter 328 is divided into two in the circumferential direction as shown in FIG. 48, and each divided part includes a filter 328a that transmits the visible band and a red A filter 328b that transmits the outer band is arranged. Therefore, the band-limiting filter 328 selectively transmits either the visible band or the infrared band of the light emitted from the light source 24.
Note that the rotation of the drive motor 327 is controlled by a motor driver 29 that is controlled by the control section 25.

The light transmitted through the band-limiting filter 328 is
The light is incident on the cable 4 and the light guide 33 inserted into the insertion section 2, and the light guide 33
The light is guided to the distal end 9 through the distal end 9, and is emitted from a light distributing lens system 34 provided at the distal end 9 to illuminate the object to be observed.

On the other hand, at the imaging position of the objective lens system 35 provided at the tip 9, a solid-state image pickup device 336 as an image pickup means is arranged. This solid-state image sensor 336 has sensitivity at least in the visible band and infrared band.

Further, in front of the imaging surface of the solid-state image sensor 336, a color filter 33 is provided as a wavelength region dividing means.
7 are arranged. This color filter 337 is
As shown in Figure 50, different wavelength regions
Filters 337a and 33 that transmit R0, G0, and B0
7b and 337c are arranged in, for example, a mosaic pattern.

In this embodiment, each of the filters 337a, 33
7b and 337c have double transmission characteristics, and have transmission wavelength regions in the visible band and infrared band. That is, as shown in FIG. 51, the filter 337a
transmits red light R in the visible band and infrared light IR3 in the infrared band, and the filter 337b
The filter 337c transmits green light G in the visible band and infrared light IR2 in the infrared band, and filters blue light B in the visible band and infrared light in the infrared band.
It is designed to pass through IR1. Note that the infrared rays IR1, IR2, and IR3 have different wavelength ranges, and the center wavelengths of IR1, IR2, and IR3 become longer in this order.

In this embodiment, the transmission wavelength range of each of the filters 337a, 337b, and 337c of the color filter 337 is limited by the band-limiting filter 328 to a wavelength range that belongs to either the visible band or the infrared band. That is, the band limiting filter 3
If the visible band is selected by 28, the infrared band is not illuminated, so the color filter 33
7 famous filters 337a, 337b, 337c
transmits B, G, and R in the visible band, respectively; on the other hand, when the infrared band is selected by the band limiting filter 328, the visible band is not illuminated, so each filter of the color filter 337 33
7a, 37b, 37c are in the infrared band, respectively.
It will pass through IR1, IR2, and IR3. The light transmitted through each of the filters 337a, 337b, and 337c is received by the solid-state image sensor 336 and photoelectrically converted. Signals corresponding to each pixel of the solid-state image sensor 336 are input to a video signal processing section 338, and subjected to signal processing corresponding to the simultaneous method. In this video signal processing section 338, a signal corresponding to each pixel of the solid-state image sensor 336 is subjected to video signal processing according to the front surface of each pixel and the type of filters 337a, 337b, and 337c. For example, filter 337
The pixel signal corresponding to a is red (R), and the filter 337
The pixel signal corresponding to b is green (G), and the filter 337
Each color of blue (B) is assigned to the image signal corresponding to c, and the image signal is processed. The video signal output from the video signal processing section 338 is input to the color CRT monitor 7, so that the object to be observed is displayed in color.

In this embodiment configured as described above, when the light source lighting device 26 is turned on by the control unit 25, the light source 24 emits light including visible light and infrared light. A band-limiting filter 228 selectively transmits only the variable band or the infrared band of the light emitted from the light source 24 . Then, the light transmitted through this band-limiting filter 228 is irradiated onto the object to be observed.

The reflected light from the observed object corresponding to this irradiation light passes through a color filter 337 arranged in front of the solid-state image sensor 336, and is received by the solid-state image sensor 336.
337b and 337c have transmission wavelength regions in the visible band and infrared band, and when the visible band is selected by the band limiting filter 328, each filter 337 of the color filter 337
a, 337b, and 337c transmit visible band B, G, and R, respectively; on the other hand, when the infrared band is selected by the band limiting filter 328, each filter 337 of the color filter 337
a, 337b, and 337c are in the infrared band, respectively.
Transmits IR, IR2, and IR3.

The light incident on the solid-state image sensor 336 is photoelectrically converted, a video signal is generated in a video signal processing section 338, and the object to be observed is displayed in color on the color CRT monitor 7. That is, when the visible band is selected by the band-limiting filter 328, an image in the general visible range of the object to be observed is displayed; on the other hand, when the band-limiting filter 328 selects the infrared band. In this case, the image of the object to be observed in the infrared region will be displayed in pseudo color.

According to this embodiment, by switching the band limiting filter 328, either the visible band or the infrared band is selected depending on the object to be observed, and the object to be observed can be displayed in color. can do. Therefore, it is possible to select the optimum observation wavelength band according to the object to be observed, and it becomes easy to detect the difference in color tone of each part of the object to be observed, which is difficult to distinguish using images in a general visible range.

Note that each filter 337 of the color filter 337
As shown in FIG. 50, a, 337b, and 337c are not limited to those that transmit R, G, and B, respectively, in the visible band; Cy) may be transmitted.

FIG. 52 is an explanatory diagram showing the transmission characteristics of each filter of the color filter according to the 15th embodiment of the present invention.

Each of the filters 337a, 337b, and 337c of the color filter 337 in this embodiment has red light R, infrared band IR,
Green light G and infrared band IR, blue light R and infrared band IR
It is becoming more transparent.

Further, when the visible band is selected by the band-limiting filter 328, the video signal processing unit 338 performs video signal processing on the output signal of the solid-state image sensor 336 as a color image; Therefore, when the infrared region is selected, the output signal of the solid-state image sensor 336 is subjected to video signal processing as a monochrome image. The other configurations are the same as those of the 18th embodiment.

In this embodiment, by switching the band limiting filter 328, a color image in the visible band and a monochrome image in the infrared band can be selectively displayed depending on the object to be observed.

In this embodiment, the filters 337a, 337b, 337b of the color filter 337 are easier to form than the color filter having the transmission characteristics shown in FIG. 51, and can be realized at low cost.

Note that each filter 337 of the color filter 337
a, 337b, and 337c are not limited to those that transmit R, G, and B, respectively, in the visible band, as shown in FIG. 52; for example, as shown in FIG. ),green
(G) and cyan (Cy) may be transmitted.

FIG. 53 is an explanatory diagram showing a light source section in a 16th embodiment of the present invention.

In this embodiment, the band limiting filter 340 is
It is provided so that it can be inserted and removed freely between the light source 24 and the proof optical path in the embodiment. The band limiting filter 340
As shown in FIG. 35, this has a narrow band pass characteristic centered at 805 nm.
Note that the transmission wavelength band of this band-limiting filter 240 is
W0 is preferably as narrow as possible, approximately 40 nm or less.

The other configurations are the same as those of the 15th embodiment.

As shown in Figure 36, blood mixed with ICG has a maximum absorption at 805 nm. Therefore, for example, ICG is mixed into the blood by intravenous injection, and the infrared band is selected by the band limiting filter 328.
When the band-limiting filter 340, which has a bandpass characteristic centered on 805 nm with maximum absorption rate, is interposed in the illumination optical path of the light source 24, the object to be observed is irradiated with a narrow band of light centered on 805 nm. is,
An image of the object to be observed in this narrow band is observed.
Light centered at 805 nm reaches deep into the mucous membrane and is absorbed in blood vessels, so the blood vessels are observed as shadows. Therefore, the running state of blood vessels can be observed with much better contrast than when observing in other wavelength ranges.

Note that the band-limiting filter 340 is connected to the light source 24.
The effect when evacuated from the illumination optical path is the same as in the fourteenth embodiment. Further, the color filter 337 is not limited to the one shown in FIG. 52, but may be one having the transmission characteristics shown in FIG. 34, for example.

Incidentally, instead of inserting the band-limiting filter 340 into the illumination optical path, as shown in FIG.
A light source 341 such as a laser or LED that emits light in a narrow band centered on 805 nm is prepared, and when observing an object image in a narrow band centered on 805 nm, the light source 24 that emits light in a wide band is prepared. Alternatively, the light source 341 may be used.

FIG. 55 is an explanatory diagram showing the transmission characteristics of a narrowband band-limiting filter in the seventeenth embodiment of the present invention.

This embodiment uses the color filter 3 in the 15th embodiment.
37 filters 337a, 337b, 337c
The transmission characteristics of filter 3 are as shown in FIG.
37a transmits R in the visible band and a narrow band centered at 805 nm, and the filter 337b is
The filter 337c transmits G in the visible band and a narrow band centered at 805 nm, and the filter 337c transmits B in the visible band and a narrow band centered at 805 nm.

The other configurations are the same as those of the 15th embodiment.

In this embodiment, when the band-limiting filter 328 selects the visible band, a color image in the normal visible band is obtained, whereas when the band-limiting filter 328 selects the infrared band, an infrared image is obtained. Light is irradiated onto the object to be observed, and only a narrow band of light centered around 805 nm is transmitted through the color filter 337,
An image of the object to be observed in this narrow band is observed.

The filters that transmit a narrow band centered on 805 nm are filters 337a, 337b, and 337.
For example, one filter may have the above-mentioned narrow band transmission characteristic.

56 to 58 relate to the 18th embodiment of the present invention, FIG. 56 is an explanatory diagram showing a band limiting filter, FIG. 57 is an explanatory diagram showing the transmission characteristics of each filter of the band limiting filter, and FIG. The figure is an explanatory diagram showing the transmission characteristics of each filter of the rotating filter.

In this embodiment, a band-limiting filter 351 as shown in FIG. 56 is provided in place of the band-limiting filter 328 in the fourteenth embodiment. Each filter 351a of this band limiting filter 351,
As shown in FIG. 57, 351b is a filter that transmits visible band and ultraviolet band, respectively. In addition, each filter 337 of the color filter 337
As shown in FIG. 58, a, 337b, and 337c have transmission wavelength regions in the visible band and the ultraviolet band. That is, the filter 337a transmits red light R and UV3 in the ultraviolet band, the filter 337b transmits green light G and UV2 in the ultraviolet band, and the filter 337c transmits blue light R and ultraviolet light in the ultraviolet band. It is designed to transmit UV3. Note that the ultraviolet light UV1,
UV2 and UV3 have different wavelength ranges, UV1,
The center wavelength becomes longer in the order of UV2 and UV3.

In this embodiment, by switching the band limiting filter 351, either the visible band or the ultraviolet band can be selected depending on the object to be observed, and the object to be observed can be displayed in color. Therefore, it is possible to observe color tone differences in each part of the object to be observed in the ultraviolet band, which cannot be observed with images in the general visible range.

FIG. 59 is an explanatory diagram showing an endoscope apparatus according to the present invention and a nineteenth embodiment.

In this embodiment, the imaging device of the 14th embodiment is applied to an external television camera attached to the eyepiece of a fiberscope.

The fiber scope 60 is the fifth embodiment and the thirteenth embodiment.
Since the configuration is similar to that shown in the embodiment, the explanation will be omitted.

The eyepiece section 65 of the fiberscope 60 includes:
An external television camera 370 is detachably attached. This external TV camera 3
70 includes an imaging lens 371 that forms an image of the light from the eyepiece section 65, and a solid-state image sensor 336 disposed at the imaging position of this imaging lens 371. A color filter 337 having transmission characteristics in the visible band and infrared band is provided on the front surface of the solid-state image sensor 336, as in the fourteenth embodiment. Further, the light emitted from the light source 24 is passed through a band-limiting filter 3 that selectively transmits the visible band and the infrared band.
28 and enters the incident end of the light guide 69 of the fiberscope 60.

Other configurations, functions, and effects are the same as those of the fourteenth embodiment.

In this embodiment, the combination of color filters and band limiting filters is not limited to that shown in the 14th embodiment, but may be the combination shown in the 15th to 18th embodiments.

In the fourteenth to nineteenth embodiments described above, a filter that can selectively transmit three or more bands such as an ultraviolet band, a visible band, and an infrared band is used as a band limiting filter, and each filter 337 of the color filter 337
Select any observation wavelength band from among the three or more observation wavelength bands by using filters a, 337b, and 333c that have transmission wavelength regions in three or more selectable bands of the band limiting filter. It may be possible to do so.

In addition, the observation wavelength band that can be selected is not limited to those divided into ultraviolet, visible, and infrared. You can set it as you like.

Furthermore, the band limit filter and color filter are
It is only necessary to arrange the light source 24 and an imaging means such as the solid-state imaging device 336, and the arrangement order can be arbitrarily determined.

60 to 65 relate to the 20th embodiment of the present invention, FIG. 60 is a block diagram showing the configuration of an imaging device, FIG. 61 is an explanatory diagram showing a color separation filter, and FIG. 62 is a color separation FIG. 63 is an explanatory diagram showing the transmission characteristics of each filter of the filter; FIG. 64 is an explanatory diagram showing the transmission characteristics of the filter interposed in the observation optical path;
The figure is an explanatory diagram showing the transmission characteristics of a visible transmission filter.
FIG. 65 is an explanatory diagram showing the transmission characteristics of a near-infrared bandpass filter.

In this embodiment, a lamp 407 to which power is supplied by a power source 406 is provided within the control device 6 . This lamp 407 is designed to emit light in a wide range of wavelengths from visible to infrared light. Between the lamp 407 and the entrance end of the light guide 33 of the electronic endoscope 1, a visible transmission filter 421 and a near-infrared bandpass filter are inserted into and removed from the illumination optical path individually by a filter changer 423. A filter 422 is provided. The visible transmission filter 421 transmits visible light, as shown in FIG. 64, and the near-infrared bandpass filter 422 has transmission characteristics that transmit only near-infrared light, as shown in FIG. 65. have. Also,
The filter changer 423 is controlled by a control circuit 420.

On the other hand, an objective lens system 401 is provided at the distal end 9 of the electronic endoscope 1.
A solid-state image sensor 404 is disposed at the imaging position. This solid-state image sensor 404 has sensitivity at least in the visible to near-infrared light range. A color separation filter 4 is provided in front of the solid-state image sensor 404.
03 is provided. This color separation filter 40
3, as shown in FIG. 61, each color filter 403a, 403b, 403c transmits cyan (Cy), green (G), and yellow (Ye) in the visible band.
are arranged in a mosaic pattern. Also,
Each color filter 403 of the color separation filter 403
As shown in FIG. 62, elements a, 403b, and 403c have a double transmission characteristic of transmitting not only Cy, G, and Ye in the visible band but also infrared light.

Further, as shown in FIG. 63, a filter 402 is provided between the objective lens system 401 and the solid-state image sensor 404, which has a characteristic of transmitting the visible band and a narrow band centered around 805 nm.

The solid-state image sensor 404 is driven by a driver 410 in the control device 6, and the read signal is amplified by a preamplifier 411 and then input to a process circuit 412, where it is subjected to gamma correction, white balance, matrix processing, etc. signal processing is now being performed. The video signal from this process circuit 412 is input to an NTSC encoder 413,
The signal is converted to an NTSC video signal and input to the monitor 7.

Note that the control circuit 420 and the driver 4
10, process circuit 412, NTSC encoder 4
13 is periodized by a timing generator 415 which generates a periodic signal for the entire system.

In this embodiment, a lamp 407 emits light in the visible to infrared range using power from a power source 406, and this light is transmitted to the distal end 9 of the electronic endoscope 1 via the light guide 33. and illuminates the subject. Then, the returned light from the object due to this illumination light is imaged by the objective lens system 401 onto the solid-state image sensor 404, and the solid-state image sensor 40
4, the subject image is captured.

Here, when the filter changer 423 is driven under the control of the control circuit 420 and only the visible transmission filter 421 is inserted in the illumination optical path, the light emitted from the lamp 407 passes through the visible transmission filter 421. street, visible light,
This visible light is irradiated onto the subject. The returned light from the object caused by the illumination light passes through a filter 402 and is color-separated by a color separation filter 403, and then read out as a video signal by a solid-state image sensor 404. The output signal of this solid-state image sensor 404 is processed by a preamplifier 411, a process circuit 412, and an NTSC encoder 413.
The visible image is displayed in color.

On the other hand, under the control of the control circuit 420, the filter engine 423 is driven,
When only the near-infrared bandpass filter 422 is installed in the illumination optical path, the light emitted from the lamp 407 passes through the near-infrared bandpass filter 422 and is converted into near-infrared light. The subject is illuminated. The returned light from the subject due to this illumination light is incident on a filter 402, and only light in a narrow band centered around 805 nm is transmitted through the filter 402. This narrow band light is passed through a color separation filter 4.
03, the signal passes through this color separation filter 403 without being color separated, and is read out as a video signal by the solid-state image sensor 404. This solid-state image sensor 404
The output signal is processed by a preamplifier 411, a process circuit 412, and an NTSC encoder 413. Then, the subject image in a narrow band centered at 805 nm is displayed as a monochrome image on the monitor 7.

As described above, according to this embodiment, as in the other embodiments, it is possible to obtain a normal visible color image and also to obtain a narrow band infrared image centered at 805 nm. Therefore, as in the 9th and 16th embodiments, by mixing ICG into blood and observing a narrow band infrared image centered at 805 nm, observation with visible light is difficult or impossible. It becomes possible to observe the course of blood vessels under the mucosa and the extent of lesions deep within the mucosa. In addition, when performing treatment with YAG laser, 805 nm in the infrared light region
By providing a filter 402 in front of the solid-state image sensor 404 that has transmission characteristics that transmit only near-infrared light centered on
Another advantage is that the observation screen is not disturbed by the light.

66 to 68 relate to the 21st embodiment of the present invention, in which FIG. 66 is a block diagram showing the configuration of an image sensor, FIG. 67 is an explanatory diagram showing a rotary filter, and FIG.
FIG. 8 is an explanatory diagram showing the transmission characteristics of each filter of the rotary filter.

As shown in FIG. 66, the insertion section 2 of the electronic endoscope 1 includes a light guide 114 that transmits illumination light.
is inserted. The distal end surface of the light guide 114 is disposed at the distal end 9 of the insertion section 2, and illumination light can be emitted from the distal end 9. Further, the incident end side of the light guide 114 is inserted into the universal cord 4 and connected to the connector 5. Further, the tip portion 9 is provided with an objective lens system 115, and a solid-state image sensor 116 is located at the imaging position of the objective lens system 115.
is installed. This solid-state image sensor 116 is
It has sensitivity in a wide wavelength range from the ultraviolet region to the infrared region, including the visible region. The solid-state image sensor 1
Signal wires 126 and 127 are connected to 16, and these signal wires 126 and 127 are inserted into the insertion portion 2 and the universal cord 4 and connected to the connector 5.

On the other hand, inside the control device 6, a lamp 121 is provided that emits light in a wide band ranging from ultraviolet light to infrared light. As this lamp 121, a general xenon lamp, a strobe lamp, or the like can be used. The xenon lamp and strobe lamp emit large amounts of not only visible light but also ultraviolet light and infrared light. This lamp 121 is configured to be supplied with electric power by a power supply section 122. A rotary filter 450 that is rotationally driven by the motor 123 is disposed in front of the lamp 121 . As shown in FIG. 67, this rotary filter 450 has filters 450a, 450b, 450c on the outer periphery that transmit R, G, and B, respectively.
are arranged along the circumferential direction, and on the inner circumferential side, filters 450d that transmit ultraviolet light range UV1,
A filter 450e having bandpass characteristics of a narrow band IR1 centered at 805 nm and a filter 450f transmitting infrared light IR2 of 900 nm or more are arranged along the circumferential direction. Incidentally, the transmission characteristics of each of the filters 450a to 450f are shown in FIG. 68.

Further, the motor 123 is connected to the motor driver 1
25, the rotation is controlled and driven.

In this embodiment, a filter switching device 451 controlled by switching circuit 143 is provided. This filter switching device 451 is configured to switch the rotary filter 450 such that either the outer circumferential side or the inner circumferential side of the rotary filter 450 is interposed in the illumination optical path between the lamp 121 and the incident end of the light guide 114. and a motor 123.

The light transmitted through the rotary filter 450 enters the incident end of the light guide 114, is guided to the tip 9 through the light guide 114, and is emitted from the tip 9 to illuminate the observation site. It's getting old.

The returned light from the observation site due to this illumination light is transmitted to the solid-state image sensor 116 by the objective lens system 115.
An image is formed on top and photoelectrically converted. This solid-state image sensor 116 includes the signal line 1
A drive pulse from a driver circuit 178 in the control device 6 is applied via 26, and reading and transfer are performed by this drive pulse. The video signal read out from the solid-state image sensor 116 is input to a preamplifier 132 provided in the control device 6 or the electronic endoscope 1 via the signal line 127. The video signal amplified by this preamplifier 132 is input to a process circuit 133, where it is subjected to signal processing such as γ correction and white balance.
The converter 134 converts the signal into a digital signal. This digital video signal is selected by a select circuit 135 controlled by the switching circuit 143 to select, for example, red (R), green (G),
Three memories (1) 136a corresponding to each color of blue (B),
The information is selectively stored in memory (2) 136b and memory (3) 136c. Said memory (1) 13
6a, memory (2) 136b, memory (3) 136c,
They are simultaneously read out, converted into analog signals by the D/A converter 137, and output as R, G, and B color signals, and are also input to the encoder 138, which outputs them as NTSC composite signals. It's becoming like that.

Then, the R, G, B color signal or NTSC
The composite signal is input to a color monitor 7, which displays the observed region in color.

Also, within the control device 6, there is a timing generator 142 that generates the timing of the entire system.
is provided, and this timing generator 142
Accordingly, each circuit such as the motor driver 125 and the driver circuit 178 is synchronized.

In this embodiment, the switching circuit 143 controls the filter switching device 451, and the rotary filter 450
The outer peripheral side of the lamp 121 and the light guide 114
When interposed in the illumination optical path between the input end and the input end, the light emitted from the lamp 121 passes through the filter 450 that passes through R, G, and B of the rotary filter 450.
a, 450b, 450c sequentially, R,
The light is divided in time series into light in the G and B wavelength regions. The R, G, and B lights are then transmitted to the tip 9 via the light guide 114 and irradiated onto the subject. R, G, B in this visible band
The return light from the object caused by the field sequential illumination light is imaged by the objective lens system 115 onto the solid-state image sensor 452, and the object image is captured by the solid-state image sensor 452. Therefore, a normal visible image is displayed in color on the monitor 7.

On the other hand, when the filter switching device 451 is controlled by the switching circuit 143 and the inner peripheral side of the rotary filter 450 is interposed in the illumination optical path between the lamp 121 and the incident end of the light guide 114, the lamp 121 The light emitted from the rotary filter 450 passes through the filter 4 that transmits UV1, IR1, and IR2.
Pass through 50d, 450e, 450f sequentially,
The light is divided chronologically into UV1, IR1, and IR2 wavelength ranges. And this light is Ride Guide 1
The light is transmitted to the tip 9 via the light source 14 and irradiated onto the subject. The returned light from the subject due to this illumination light is transmitted to the solid-state image sensor 4 by the objective lens system 115.
52 , and a subject image is captured by this solid-state image sensor 452 . Therefore, on the monitor 7, images in the invisible regions of the ultraviolet and infrared light regions in the UV1, IR1, and IR2 wavelength regions are displayed in pseudo color. Note that the memories 136a, 136b, 13
By selectively reading out one or two of 6c, it is also possible to obtain an image in one or two wavelength regions of UV1, IR1, and IR2.

As described above, according to this embodiment, as in the other embodiments, it is possible to obtain a normal visible color image, and also to obtain an image in an invisible region in the ultraviolet and infrared light regions.

Note that the transmission wavelength range of each filter provided on the outer circumferential side and the inner circumferential side of the rotary filter 450 is not limited to this embodiment, and can be arbitrarily set.

It should be noted that the present invention is not limited to the above-mentioned embodiments, and, for example, the present invention is not limited to one that receives reflected light from an object to be observed, but may also be one that receives light that has passed through an object to be observed.

Further, the present invention can be applied to devices other than endoscopes. [Effects of the Invention] As explained above, according to the present invention, the visible light region includes a filter device for obtaining light in a wavelength region other than visible light. , there is no need to place it inside the tip of the endoscope insertion section, which is required to be smaller in diameter. Visible information can be obtained by selecting the illumination light in the optimal wavelength range according to the body, and it is possible to easily detect color tone differences in each part of the observed object that are difficult to distinguish with images in the general visible range. In addition, by selectively irradiating the object with only the illumination light in the necessary wavelength range, the temperature of the endoscope insertion section tip region of the endoscope insertion section is prevented from rising due to illumination light in the unnecessary wavelength range. There is an effect that can be done.

[Brief explanation of the drawing]

1 to 6 relate to a first embodiment of the present invention, and FIG. 1 is a block diagram showing the configuration of an imaging device;
Fig. 2 is a side view showing the entire electronic endoscope device, Fig. 3 is an explanatory view showing the band switching filter, Fig. 4 is an explanatory drawing showing the rotary filter, and Fig. 5 is an illustration of each filter of the band switching filter. FIG. 6 is an explanatory diagram showing the transmission wavelength band, FIG. 6 is an explanatory diagram showing the transmission characteristics of each filter of the rotary filter, FIGS. 9
The figures to FIG. 11 relate to the third embodiment of the present invention,
FIG. 9 is a block diagram showing an imaging device, FIG. 10 is an explanatory diagram showing a rotary filter, FIG. 11 is a timing chart for explaining the operation of this embodiment, and FIGS. Regarding the fourth embodiment, FIG. 12 is a block diagram showing the imaging device;
FIG. 3 is an explanatory diagram showing a rotary filter, FIG. 14 is a timing chart for explaining the operation of this embodiment, FIG. 15 is an explanatory diagram showing changes in spectral characteristics of blood due to ICG contamination, and FIGS. 16 to 18 The figures relate to a fifth embodiment of the present invention, with FIG. 16 being an explanatory diagram showing the configuration of an endoscope device, FIG. 17 being an explanatory diagram showing a rotary filter, and FIG. 18 being an explanatory diagram showing the operation of this embodiment. Timing chart for Figures 19 to 2
Fig. 1 relates to the sixth embodiment of the present invention, Fig. 19 is an explanatory diagram showing the configuration of the imaging device, Fig. 20 is a front view of the band switching mirror, and Fig. 21 shows the reflection characteristics of each mirror of the band switching mirror. 22 is an explanatory diagram showing the 6th
An explanatory diagram showing a modification of the light source section in the embodiment, FIG. 23 is a front view of a band switching mirror in a modification of the sixth embodiment, and FIGS. 24 and 25 relate to a seventh embodiment of the present invention, FIG. 24 is an explanatory diagram showing a light source section, FIG. 25 is an explanatory diagram showing a rotating filter, FIGS. 26 to 30 are related to the eighth embodiment of the present invention, and FIG. 26 is a block diagram showing an imaging device. , second
Figure 7 is an explanatory diagram showing the band-limiting filter, Figure 28 is an explanatory diagram showing the transmission characteristics of each filter in the band-limiting filter, Figure 29 is an explanatory diagram showing the rotary filter, and Figure 30 is an explanatory diagram showing the transmission characteristics of each filter in the rotary filter. An explanatory diagram showing the transmission characteristics. FIG. 31 is an explanatory diagram showing the transmission characteristics of each filter of a modified example of the rotary filter in the eighth embodiment. FIGS. 32 and 33 are a modification of the band limiting filter in the eighth embodiment. 34 to 36 are explanatory diagrams showing examples, and FIG. 34 is an explanatory diagram showing a light source section, and FIG.
Figure 5 is an explanatory diagram showing the transmission characteristics of a narrowband band-limiting filter, and Figure 36 is an illustration of blood mixed with ICG and ICG.
An explanatory diagram showing the difference in spectral characteristics of blood that is not contaminated with
FIG. 37 is an explanatory diagram showing the light source section in a modification of the ninth embodiment, FIG. 38 is an explanatory diagram showing the transmission characteristics of each filter of the rotary filter in the tenth embodiment of the present invention, and FIGS. The figures relate to the eleventh embodiment of the present invention, FIG. 39 is an explanatory diagram showing a rotary filter, FIG. 40 is an explanatory diagram showing the transmission characteristics of each filter of the rotary filter, and FIGS. 41 to 44 are explanatory diagrams showing the present invention 41 is an explanatory diagram showing a band-limiting filter, FIG. 42 is an explanatory diagram showing the transmission characteristics of each filter of the band-limiting filter, and FIG. 43 is an explanatory diagram showing the transmission characteristics of each filter of the band-limiting filter.
FIG. 44 is an explanatory diagram showing a rotating filter, FIG. 44 is an explanatory diagram showing transmission characteristics of each filter of the rotating filter,
FIG. 45 is an explanatory diagram showing the configuration of an endoscope device according to the thirteenth embodiment of the present invention, FIGS. 46 to 51 are related to the fourteenth embodiment of the present invention, and FIG. 47 is an explanatory diagram showing the light emission characteristics of the light source; FIG. 48 is an explanatory diagram showing the band-limiting filter; FIG. 49 is an explanatory diagram showing the transmission characteristics of each filter in the band-limiting filter; FIG. 50 is an explanatory diagram showing a color filter, FIG. 51 is an explanatory diagram showing the transmission characteristics of each filter of the color filter, and FIG.
53 is an explanatory diagram showing the transmission characteristics of each filter of the color filter according to the 15th embodiment of the present invention, FIG. 53 is an explanatory diagram showing the light source section in the 16th embodiment of the present invention, and FIG. FIG. 55 is an explanatory diagram showing the light source section in a modified example of the present invention. FIG. Regarding the 18th embodiment, Fig. 56 is an explanatory diagram showing a band-limiting filter, Fig. 57 is an explanatory diagram showing the transmission characteristics of each filter of the band-limiting filter, and Fig. 58 is an explanatory diagram showing the transmission characteristics of each filter of the rotary filter. Explanatory diagram, 5th
FIG. 9 is an explanatory diagram showing an endoscope device according to a nineteenth embodiment of the present invention, FIGS. 60 to 65 are related to a twentieth embodiment of the present invention, and FIG. 60 shows the configuration of an imaging device. Block diagram, Fig. 61 is an explanatory diagram showing the color separation filter, Fig. 62 is an explanatory diagram showing the transmission characteristics of each filter of the color separation filter, and Fig. 63 is an explanatory diagram showing the transmission characteristics of the filter installed in the observation optical path. Explanatory diagram,
Fig. 64 is an explanatory diagram showing the transmission characteristics of a visible transmission filter, Fig. 65 is an explanatory diagram showing the transmission characteristics of a near-infrared bandpass filter, and Figs. 66 to 68 relate to the 21st embodiment of the present invention. , FIG. 66 is a block diagram showing the configuration of the imaging device, FIG. 67 is an explanatory diagram showing a rotating filter, and FIG. 68 is an explanatory diagram showing the transmission characteristics of each filter of the rotating filter. 1... Electronic endoscope, 21... Imaging device, 22...
...Light source unit, 24...Light source, 27...Band switching filter, 31...Rotary filter, 36...Solid-state image sensor, 37...Video signal processing unit.

Claims (1)

[Scope of Claims] 1. Illumination means for switching illumination light in a visible light region or at least illumination light in a wavelength region other than the visible light region; An imaging means that is sensitive to a wavelength range other than the optical range, a means for obtaining a visible color image from an image obtained by the imaging means, and a means for obtaining an image containing at least information in a wavelength range other than the visible light range. An endoscope imaging device comprising: and means for selectively displaying at least one of the images.