JP5331855B2 - Endoscopic diagnosis device - Google Patents

Endoscopic diagnosis device Download PDF

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JP5331855B2
JP5331855B2 JP2011186345A JP2011186345A JP5331855B2 JP 5331855 B2 JP5331855 B2 JP 5331855B2 JP 2011186345 A JP2011186345 A JP 2011186345A JP 2011186345 A JP2011186345 A JP 2011186345A JP 5331855 B2 JP5331855 B2 JP 5331855B2
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light
autofluorescence
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light source
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JP2013046687A (en
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拓明 山本
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富士フイルム株式会社
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Abstract

<P>PROBLEM TO BE SOLVED: To provide an endoscopic diagnostic apparatus that provides an autofluorescence image from which the effects of light absorption by blood is eliminated, without the need to use a fluorescence probe. <P>SOLUTION: The endoscopic diagnostic apparatus includes: a light source unit for emitting white light, and one or more kinds of excitation light having different central wavelengths for causing at least one autofluorescent substance contained in an observation region of a subject to emit one or more kinds of autofluorescence; an imaging unit for receiving reflected light of the white light from the observation region of the subject to image a reflected light image when the observation region of the subject is illuminated with the white light from the light source unit, and receiving autofluorescence emitted from the autofluorescent substance to image an autofluorescence image when the observation region of the subject is irradiated with the excitation light from the light source unit; and an image correction unit which has correction coefficients for correcting decrease in a signal intensity of the autofluorescence image occurring in accordance with the amount of the blood, the decrease being caused when the autofluorescence image emitted from the autofluorescent substance is absorbed by the blood, and which is adapted to obtain the correction coefficient corresponding to a reflectance of the reflected light image from among the correction coefficients, and uses the obtained correction coefficient to correct the signal intensity of the autofluorescence image. <P>COPYRIGHT: (C)2013,JPO&amp;INPIT

Description

  The present invention relates to an endoscopic diagnostic apparatus that captures autofluorescence emitted from an autofluorescent substance contained in an observation region (living body) of a subject and acquires an autofluorescence image.

  Conventionally, normal light (white light) emitted from a light source device is guided to the distal end portion of the endoscope, irradiated on the subject's observation area, and the reflected light is imaged to obtain a normal light image (white light image). Is used, and an endoscope apparatus that performs normal light observation (white light observation) is used. On the other hand, in recent years, in addition to normal light observation, excitation light (special light) for autofluorescence observation is irradiated to the subject's observation area, and the autofluorescence emitted from the autofluorescent material is imaged and the autofluorescence is imaged. An endoscope apparatus that acquires a fluorescent image (special light image) and performs autofluorescence observation (special light observation) is used.

  As an endoscope apparatus for performing autofluorescence observation, for example, there is Patent Document 1.

  In Patent Document 1, an etalon that includes two excitation lights and whose transmission wavelength range can be changed is provided on the front surface of the sensor, and an image is obtained from a fluorescence image captured in a wavelength region that matches the fluorescence wavelength of the target substance in each excitation light. Describes an endoscope device that performs calculations, extracts images of collagen / elastin, porphyrin, and fluorescent probe, assigns collagen / elastin to the R channel, assigns porphyrin to the G channel, and assigns the fluorescent probe to the B channel and performs pseudo color display. Has been.

  In Patent Document 1, as shown in FIGS. 19 and 20, first, a wavelength region in which excitation light A having a wavelength of 405 nm is irradiated on the subject in the first and second frames and emitted from collagen and elastin in the first frame. The image signal D1 including the autofluorescence of a1 and the autofluorescence component of the wavelength region a2 emitted from the porphyrin is acquired, and the image signal D2 including the autofluorescence component of the wavelength region a1 is acquired in the second frame. In a subsequent third frame, the subject is irradiated with excitation light B having a wavelength of 660 nm, and an image signal D3 including a fluorescence component in the wavelength region a3 emitted from the fluorescent probe is acquired.

  After the image signals D1 to D3 are acquired, the image signal E1 having only the fluorescent component in the wavelength region a2 is generated by subtracting the image signal D2 from the image signal D1. The image signal D2 is assigned to the R channel, the image signal E1 is assigned to the G channel, and the image signal D3 is assigned to the B channel, so that the fluorescent image is displayed in a pseudo color manner. As a result, as shown in Table 1 below, the fluorescence image is displayed in a color-coded manner in which the normal part is yellow, the inflamed part is gray, and the lesioned part is magenta according to the state of the living tissue.

JP 2009-95683 A

  The method of Patent Document 1 darkens using the fact that the amount of blood increases in the inflamed part, the autofluorescence is absorbed by the blood, and the signal intensity (fluorescence intensity) of the autofluorescence decreases according to the amount of blood. This area is extracted as an inflamed part.

  However, the method of Patent Document 1 cannot distinguish between an inflamed part and an area with a large amount of blood such as a thick blood vessel that is not an inflamed part. I don't know what you are looking at. In addition, the amount of blood similarly increases in the lesioned part, so that the signal intensity decreases. In order to avoid this, in Patent Document 1, it is necessary to enhance the fluorescence intensity using a fluorescent probe, and there is a problem that the autofluorescence emitted from the autofluorescent material cannot be fully utilized.

  An object of the present invention is to provide an endoscopic diagnostic apparatus capable of obtaining an autofluorescence image in which the influence of light absorption by blood is eliminated without using a fluorescent probe.

In order to achieve the above object, the present invention provides one or more different center wavelengths for emitting one or more autofluorescences from a plurality of autofluorescent substances contained in white light and a subject's observation region. A light source unit that emits the first excitation light;
When the white light is irradiated from the light source unit onto the subject's observation area, the reflected light image of the white light from the observation area of the subject is received and a reflected light image is captured; and When the first excitation light is irradiated from the light source unit to the observation area of the subject, the self-fluorescence emitted from the autofluorescent substance contained in the observation area of the subject is received An imaging unit that captures a fluorescent image;
Correction coefficient for correcting that autofluorescence emitted from the autofluorescent material contained in the subject's observation region is absorbed by blood and that the signal intensity of the autofluorescence image is reduced according to the amount of blood A correction coefficient corresponding to the reflectance of the reflected light image is determined from the correction coefficient, the signal intensity of the autofluorescence image is corrected using the calculated correction coefficient , and the white light is A first propagation length until the imaging region receives the reflected light of the white light from the observation region of the subject and the white light reflected from the observation region of the subject, and the first excitation light Depending on the difference in the second propagation length until the imaging unit receives the autofluorescence emitted from the autofluorescent material included in the subject's observation area. The reflectance of the reflected light image and the signal intensity of the autofluorescence image There is provided an endoscopic diagnosis apparatus characterized by comprising an image correcting unit for correcting the non-linearity occurring.

  The image correction unit has a correction coefficient table in which the relationship between the reflectance of the reflected light image and the correction coefficient is stored, and corresponds to the reflectance of the reflected light image using the correction coefficient table. It is preferable to obtain a correction coefficient.

  Moreover, it is preferable that the said light source part emits the excitation light of the predetermined wavelength range of at least one of center wavelengths 405 nm and 445 nm as said 1st excitation light.

  The light source unit preferably includes a laser light source that emits the first excitation light.

  The light source unit emits the second excitation light emitted from the white light source that emits the second excitation light in a predetermined wavelength range having a central wavelength of 445 nm, and the second excitation light emitted from the white light source. And a phosphor that emits pseudo white light in a predetermined wavelength range.

  Moreover, it is preferable that the said light source part is provided with the laser light source which emits said 2nd excitation light.

  In addition, the imaging unit has an imaging element that captures the reflected light image and the autofluorescence image, and a spectral transmission characteristic that is disposed on an optical path of the imaging element and transmits light in a wavelength range corresponding to green and red. It is preferable to have a wavelength selection member.

  The wavelength selection member is preferably a color filter.

  The wavelength selection member is an etalon, and the green wavelength range is preferably 500 to 600 nm, and the red wavelength range is preferably 610 to 650 nm.

  The imaging unit includes a first imaging element that captures the reflected light image, and a spectral transmission characteristic that is disposed on an optical path of the first imaging element and transmits light in a wavelength range corresponding to blue, green, and red. A first wavelength selection member having a second imaging element that is more sensitive than the first imaging element that captures the autofluorescence image, and is disposed on an optical path of the second imaging element, according to green and red It is preferable to include a second wavelength selection member having spectral transmission characteristics that transmits light in the wavelength range.

  The first and second wavelength selection members are preferably color filters.

  The first and second wavelength selection members are etalon, and the green wavelength range is preferably 500 to 600 nm, and the red wavelength range is preferably 610 to 650 nm.

  Further, the image correction unit corrects the signal intensity of the green and red image signals of the autofluorescence image based on the reflectance of the green and red image signals of the reflected light image, respectively. preferable.

  Furthermore, it is preferable to provide a display device that displays pseudo colors by assigning the green image signal of the corrected autofluorescence image to the green channel and the red image signal to the red channel and the blue channel.

  According to the present invention, by correcting the signal intensity of the autofluorescence image using the correction coefficient corresponding to the reflectance of the reflected light image in the same wavelength region as the autofluorescence emission wavelength region, the absorption of light by the blood is improved. An autofluorescent image that is not affected can be obtained.

1 is an external view of an embodiment showing a configuration of an endoscope diagnosis apparatus according to the present invention. It is a block diagram showing the internal structure of the endoscope diagnostic apparatus shown in FIG. It is a conceptual diagram showing the mode of the front-end | tip part of the endoscope insertion part of the endoscope diagnostic apparatus shown in FIG. It is a graph of an example showing the light absorption intensity | strength characteristic of an autofluorescent substance. It is a graph of an example showing the fluorescence intensity characteristic of an autofluorescent substance. It is a graph of an example showing the fluorescence intensity characteristic of an autofluorescent substance. It is a graph which shows the extinction coefficient of an oxygenated hemoglobin and a reduced hemoglobin. It is a graph of an example showing the fluorescence intensity characteristic of FAD with and without blood. It is a graph of an example showing the relationship between a reflectance and fluorescence intensity, and the blood concentration. It is an example of a graph showing the relationship between fluorescence intensity and reflectance. It is a graph of an example showing the correction coefficient for correcting the fluorescence intensity of autofluorescence. In the graph of FIG. 5, the spectral transmission characteristics of the color filters are displayed in an overlapping manner. In the graph of FIG. 6, the spectral transmission characteristics of the color filters are displayed in an overlapping manner. In the graph of the fluorescence intensity distribution of autofluorescence when simultaneously irradiating a plurality of excitation lights having different wavelengths, the spectral transmission characteristics of the color filters are displayed in an overlapping manner. It is a graph of an example showing the relationship between the absorption coefficient of blood and the color filter in a normal sensor. It is a conceptual diagram showing the process in normal light observation mode and autofluorescence observation mode in the endoscope diagnostic apparatus shown in FIG. It is a conceptual diagram showing the effect | action of the endoscope diagnostic apparatus shown in FIG. It is a table | surface showing the fluorescence intensity of the normal part and lesioned part of FAD and a porphyrin. It is a conceptual diagram showing the effect | action of the endoscope apparatus shown to patent document 1. FIG. It is a conceptual diagram showing the process in the autofluorescence observation mode in patent document 1. FIG.

  Hereinafter, based on a preferred embodiment shown in the accompanying drawings, an endoscope diagnosis apparatus according to the present invention will be described in detail.

  FIG. 1 is an external view of an embodiment showing a configuration of an endoscope diagnosis apparatus according to the present invention, and FIG. 2 is a block diagram showing an internal configuration thereof. The endoscopic diagnosis apparatus 10 shown in these figures guides a light source device 12 that generates a plurality of lights having different wavelength ranges and light emitted from the light source device 12 to irradiate an observation area of a subject. An endoscope apparatus 14 that captures reflected light or autofluorescence from a subject, a processor apparatus 16 that performs image processing on an image captured by the endoscope apparatus 14 and outputs an endoscope image, and a processor apparatus 16 includes a display device 18 that displays an endoscopic image output from 16 and an input device 20 that receives an input operation.

  Here, the endoscope diagnostic apparatus 10 irradiates the subject with normal light (white light), images the reflected light, and displays (observes) the normal light image (white light image, reflected light image). Autofluorescence that displays normal light observation mode (white light observation mode) and excitation light (special light) for autofluorescence observation to the subject, images the autofluorescence, and displays the autofluorescence image (special light image) And an observation mode (special light observation mode). Each observation mode is appropriately switched based on an instruction input from the changeover switch 66 of the endoscope apparatus 14 or the input device 20.

  The light source device 12 includes a light source control unit 22, two types of laser light sources LD 1 and LD 2 that emit laser beams having different center wavelengths, a combiner (multiplexer) 24, and a coupler (demultiplexer) 26. ing.

  In the present embodiment, the laser light sources LD1 and LD2 emit narrowband light in a predetermined wavelength range (for example, center wavelength ± 10 nm) having center wavelengths of 405 nm and 445 nm, respectively. Laser light sources LD1 and LD2 are autofluorescent substances in living tissues, such as porphyrin, NADH (reduced form of Nicotinamide Adenine dinucleotide), NADPH (reduced form of Nicotinamide Adenine dinucleotide Phosphate), FAD (Flavin Adenine Dinucleotide), etc. It is the light source which irradiates the excitation light for making autofluorescence light from. Further, as will be described later, the laser light source LD2 is also a light source (white light source) that generates excitation light for generating white light (pseudo white light) from the phosphor.

  The laser light sources LD1 and LD2 are individually subjected to on / off control and light amount control by the light source control unit 22 controlled by the control unit of the processor device 16 described later, and the light emission timing and light amount ratio of each laser light source LD1 and LD2 are as follows. It can be changed freely. As the laser light sources LD1 and LD2, a broad area type InGaN laser diode can be used, and an InGaNAs laser diode, a GaNAs laser diode, or the like can also be used.

  The normal light source for generating the normal light is not limited to the combination of the excitation light and the phosphor, and any light source that emits white light may be used. For example, a xenon lamp, a halogen lamp, a white LED (light emitting diode) Etc. can also be used. An excitation light source for generating excitation light for autofluorescence observation is not limited to a laser light source (semiconductor laser), and excitation light having sufficient intensity to excite an autofluorescent substance to emit autofluorescence. Various light sources that can be irradiated, for example, a combination of a white light source and a band limiting filter can be used.

  In addition, the wavelength of excitation light for normal light observation (center wavelength, wavelength range of narrowband light) is not particularly limited, and all excitation light having a wavelength capable of generating pseudo white light from a phosphor can be used. It is. The wavelength of the excitation light for autofluorescence observation is not particularly limited, and all excitation light having a wavelength capable of exciting the autofluorescent material to emit autofluorescence can be used. For example, the wavelength of 370 to 470 nm is available. Light, particularly light having a wavelength of 400 to 450 nm can be preferably used.

  In the present embodiment, the normal light source and one of the excitation light sources are shared, but both may be configured as separate light sources. In this embodiment, two excitation lights having central wavelengths of 405 nm and 445 nm are used as excitation light for autofluorescence observation. However, the number of excitation lights for autofluorescence observation is not limited to two, Depending on the type of autofluorescence to be emitted, one or more excitation lights corresponding to each autofluorescent substance may be used.

  The light source device 12 and the phosphor of the present embodiment constitute the light source unit of the present invention. The light source unit of the present invention includes white light and one or more first excitation lights having different center wavelengths for emitting one or more autofluorescences from a plurality of autofluorescent substances included in the subject's observation region. It is something that emits.

  In the normal light observation mode, the light source controller 22 turns off the laser light source LD1 and turns on the laser light source LD2. Further, the light source controller 22 turns on both the laser light sources LD1 and LD2 in the auto-fluorescence observation mode.

  Laser light emitted from each of the laser light sources LD1 and LD2 is input to the corresponding optical fiber via a condenser lens (not shown), combined by a combiner 24, and demultiplexed into four systems of light by a coupler 26. Is transmitted to the connector portion 32A. The combiner 24 and the coupler 26 are configured by a half mirror, a reflection mirror, or the like. However, the present invention is not limited to this, and the laser light from each of the laser light sources LD1 and LD2 may be sent directly to the connector portion 32A without using the combiner 24 and the coupler 26.

  Subsequently, the endoscope apparatus 14 emits four systems (four lights) of light (normal light or excitation light for autofluorescence observation) from the distal end of the endoscope insertion portion inserted into the subject. And an imaging optical system of two systems (two eyes) that captures an endoscopic image of the observation region. The endoscope apparatus 14 includes an endoscope insertion section 28, an operation section 30 that performs an operation for bending and observing the distal end of the endoscope insertion section 28, and the endoscope apparatus 14 as a light source device 12 and a processor. Connector portions 32A and 32B that are detachably connected to the device 16 are provided.

  The endoscope insertion portion 28 includes a flexible soft portion 34, a bending portion 36, and a distal end portion (hereinafter also referred to as an endoscope distal end portion) 38.

  The bending portion 36 is provided between the flexible portion 34 and the distal end portion 38 and is configured to be bent by a turning operation of the angle knob 40 disposed in the operation portion 30. The bending portion 36 can be bent in an arbitrary direction and an arbitrary angle in accordance with a portion of the subject in which the endoscope apparatus 14 is used, and the endoscope distal end portion 38 is directed to a desired observation portion. be able to.

  Although not shown, various channels such as a forceps channel for inserting a tissue collection treatment instrument and the like and a channel for air supply / water supply are provided inside the operation unit 30 and the endoscope insertion unit 28. It has been.

  As shown in FIG. 3, two systems of illumination windows 42 </ b> A and 42 </ b> B that irradiate light to the observation region, and reflected light or autofluorescence 1 from the observation region are imaged on the distal end surface of the endoscope distal end portion 38. In addition to the system observation window 44, a forceps port 45 and the like are arranged.

  Two systems of optical fibers 46A and 48A are housed in the back of the illumination window 42A. The optical fibers 46A and 48A are laid from the light source device 12 to the scope distal end portion 38 via the connector portion 32A. An optical system such as a lens 50A is attached to the tip of the optical fiber 46A (on the illumination window 42A side). On the other hand, a phosphor 54A is disposed at the tip of the optical fiber 48A, and an optical system such as a lens 52A is attached to the tip of the phosphor 54A.

  Similarly, in the back of the illumination window 42B, there are two systems, an optical fiber 46B having an optical system such as a lens 50B at the tip, and an optical fiber 48B having an optical system such as a phosphor 54B and a lens 52B at the tip. An optical fiber is housed.

The phosphors 54A and 54B absorb a part of the blue laser light from the laser light source LD2 and emit a plurality of kinds of fluorescent materials (for example, YAG-based fluorescent materials, BAM (BaMgAl 10 O 17 ), etc.) that emit light from green to yellow. A fluorescent substance). When excitation light for normal light observation is irradiated onto the phosphors 54A and 54B, green to yellow excitation light (fluorescence) emitted from the phosphors 54A and 54B and the phosphors 54A and 54B are transmitted without being absorbed. Combined with the blue laser light, white light (pseudo white light) is generated.

  The illumination optical systems on the illumination window 42A side and the illumination window 42B side have the same configuration and operation, and illumination unevenness can be prevented by irradiating the illumination windows 42A and 42B simultaneously with equivalent illumination light. Different illumination light can be irradiated from the illumination windows 42A and 42B. It is not essential to have an illumination optical system that emits four systems of illumination light. For example, an illumination optical system that emits two or one system of illumination light can realize the same function.

  On the other hand, an optical system such as a lens 56 is attached to the back of the observation window 44, and a half mirror 57 is provided to the back of the lens 56. A CCD (Charge Coupled Device) image sensor that acquires image information of an observation region is provided at the tip of the optical path of the transmitted light that passes through the half mirror 57 and the tip of the optical path of the reflected light that is reflected by the half mirror 57. Imaging elements 58A and 58B such as CMOS (Complementary Metal-Oxide Semiconductor) image sensors are attached. The image sensor 58A (normal sensor) is for normal light observation, and the image sensor 58B (high sensitivity sensor) is for autofluorescence observation. Since the signal intensity (fluorescence intensity) of the autofluorescence is weak, in the present embodiment, a sensor with higher sensitivity than the image sensor 58A for normal light observation is used as the image sensor 58B for autofluorescence observation.

  Note that the light receiving light is not limited to the half mirror 57, and the received light may be distributed to the image sensor 58A or the image sensor 58B, for example, by putting a total reflection mirror in and out of the optical path of the received light.

  The image sensors 58A and 58B receive light (transmitted light and reflected light) from the lens 56 by a light receiving surface (imaging surface), photoelectrically convert the received light, and output an image signal (analog signal). Thus, a plurality of sets of pixels are arranged in a matrix, with one set of three colors of R, G, and B pixels. On the light receiving surface (on the optical path) of the image sensor 58A, the reflected light in the wavelength range of about 370 to 720 nm of the visible light from the observation region is divided into three corresponding to the R pixel, G pixel, and B pixel and transmitted. R, G, and B color filters having spectral transmission characteristics are provided. In addition, on the light receiving surface (on the optical path) of the image sensor 58B, corresponding to the R pixel and the G pixel, the excitation light is blocked and the R color and the G color of about 500 to 700 nm emitted from the autofluorescent material. R-color and G-color filters having spectral transmission characteristics that transmit autofluorescence in the wavelength range are provided.

  The image sensors 58A and 58B of the present embodiment constitute an image capturing unit of the present invention. The imaging unit of the present invention captures a reflected light image by receiving white light reflected from the subject's observation region when white light is irradiated from the light source to the subject's observation region. In addition, when excitation light for autofluorescence observation is irradiated from the light source unit to the subject observation area, the autofluorescence emitted from the autofluorescent material contained in the subject observation area is received. Thus, an autofluorescence image is taken.

  Further, the color filter constitutes the wavelength selection member of the present invention. The wavelength selection member of the present invention is disposed on the optical path of the image sensor and transmits light in a wavelength range corresponding to the G color and the R color. The wavelength selection member is not limited to the color filter described above, and for example, an etalon described in Patent Document 1 can also be used. When using an etalon, for example, the wavelength range of G color may be 500 to 600 nm, and the wavelength range of R color may be 610 to 650 nm.

  Further, in the present embodiment, two image sensors, the image sensor 58A that captures the normal light image (reflected light image) and the image sensor 58B that captures the autofluorescence image, are used. For example, one image sensor is used. It can also be used to capture both normal light images and autofluorescence images.

  Light guided from the light source device 12 by the optical fibers 46A and 46B and 48A and 48B is irradiated from the endoscope distal end portion 38 toward the observation region of the subject. Then, reflected light from the observation region irradiated with light or autofluorescence emitted from the autofluorescent material in the observation region is imaged by the lens 56 on the light receiving surfaces of the image sensors 58A and 58B, and the image sensor 58A. , 58B are photoelectrically converted and imaged. From the imaging elements 58A and 58B, an imaging signal (analog signal) of the imaged area of the subject to be imaged is output.

  Here, in the normal light observation mode, excitation light for normal light observation emitted from the laser light source LD2 is guided by the optical fibers 48A and 48B and irradiated to the phosphors 54A and 54B, and from the phosphors 54A and 54B. The emitted white light is irradiated to the subject's observation area from the illumination windows 42A and 42B. Then, the reflected light from the observation region of the subject irradiated with white light is collected by the lens 56, dispersed by the color filter, and a normal light image (reflected light image) is captured by the image sensor 58A.

  On the other hand, in the autofluorescence observation mode, excitation light for autofluorescence observation emitted from both of the laser light sources LD1 and LD2 is guided by the optical fibers 46A and 46B, and the subject's distal end portion 38 receives the subject's excitation light. Irradiated toward the observation area. Then, the autofluorescence emitted from the autofluorescent material in the observation region of the subject irradiated with the excitation light is collected by the lens 56, dispersed by the color filter, and G and R autofluorescence is captured by the image sensor 58B. An image is taken.

  Imaging signals (analog signals) of images (normal light images and autofluorescence images) output from the imaging elements 58A and 58B are input to the A / D converters 64A and 64B through the scope cables 62A and 62B, respectively. The A / D converters 64A and 64B convert image signals (analog signals) from the image sensors 58A and 58B into image signals (digital signals), respectively. The converted image signal is input to the image processing unit 70 of the processor device 16 via the connector unit 32B.

  Subsequently, the processor device 16 includes a control unit 68, an image processing unit 70, and a storage unit 72. The display device 18 and the input device 20 are connected to the control unit 68. The processor device 16 controls the light source control unit 22 of the light source device 12 based on an instruction input from the changeover switch 66 or the input device 20 of the endoscope device 14, and an image signal input from the endoscope device 14. Is processed, a display image is generated and output to the display device 18.

  The control unit 68 controls the operations of the image processing unit 70 and the light source control unit 22 of the light source device 12 based on an instruction from the changeover switch 66 of the endoscope apparatus 14 or an input device 20, for example, an instruction such as an observation mode. To do.

  Under the control of the control unit 68, the image processing unit 70 performs a predetermined process on an image signal input from the endoscope apparatus 14 according to the image type of the normal light image and the autofluorescence image based on the observation mode. Apply image processing. The image processing unit 70 includes a normal light image processing unit 70A and an autofluorescence image processing unit 70B.

  The normal light image processing unit 70A performs predetermined image processing suitable for the normal light image on the image signal (image data) of the normal light image supplied from the A / D converter 64A in the normal light observation mode. The normal light image signal (normal light image) is output (generated).

  The autofluorescence image processing unit 70B performs predetermined image processing suitable for the autofluorescence image on the image signal (image data) of the autofluorescence image supplied from the A / D converter 64B in the autofluorescence observation mode. To output (generate) an autofluorescence image signal (autofluorescence image). The autofluorescence image processing unit 70B corrects the signal intensity of the autofluorescence image based on the reflectance of the normal light image (reflected light image) to eliminate the influence of light absorption by blood from the autofluorescence image. .

  The image processing unit 70 of the present embodiment constitutes an image correction unit of the present invention. The image correction unit of the present invention corrects that autofluorescence emitted from the autofluorescent material contained in the subject's observation region is absorbed by blood and the signal intensity of the autofluorescence image decreases according to the amount of blood. A correction coefficient corresponding to the reflectance of the reflected light image is obtained from the correction coefficients, and the signal intensity of the autofluorescence image is corrected using the obtained correction coefficient.

  Further, the image correction unit further irradiates the subject observation region with white light, and the first propagation length until the reflected light of the white light from the subject observation region is received by the imaging unit. And a second propagation length until autofluorescence emitted from the autofluorescent material included in the subject observation area is received by the imaging unit. In accordance with the difference, the nonlinearity generated between the reflectance of the reflected light image and the signal intensity of the autofluorescence image is corrected.

  The image signal processed by the image processing unit 70 is sent to the control unit 68. In the control unit 68, the normal light image or a composite image of the normal light image and the autofluorescence image is displayed on the display device 18 based on the normal light image signal and the autofluorescence image signal according to the observation mode. The control unit 68 assigns the G image signal G ′ of the corrected autofluorescence image to the G channel and the R image signal R ′ to the R channel and the B channel, and displays the corrected autofluorescence image on the display device 18. To display pseudo color.

  Further, under the control of the control unit 68, the normal light image signal and the autofluorescence image signal are stored in the storage unit 72 including a memory or a storage device, for example, in units of one (one frame) image as necessary. Is done.

  Hereinafter, absorption of light by blood will be described.

  FIG. 4 is a graph showing an example of the light absorption intensity characteristic of the autofluorescent material. In the figure, the vertical axis represents the light absorption intensity (a.u .: arbitrary unit) of the autofluorescent substance, and the horizontal axis represents the wavelength (nm). This graph shows the absorption intensity characteristics of FAD and porphyrin, which are autofluorescent substances correlated with tumors. The figure also shows the center wavelengths 405 nm and 445 nm of laser light used as excitation light for autofluorescence observation in this embodiment.

  FAD has the property of absorbing light in the wavelength range of about 270-540 nm. The FAD light absorption intensity gradually increases as the wavelength increases from about 270 nm, reaches the first maximum at a wavelength of about 380 nm, then decreases gradually as the wavelength increases, and reaches a minimum at a wavelength of about 420 nm. . The absorption intensity gradually increases again as the wavelength increases from about 420 nm, reaches a second maximum at a wavelength of about 460 nm, and then gradually decreases as the wavelength increases.

  Porphyrin has the property of absorbing light in the wavelength range of about 340 to 450 nm. The light absorption intensity of porphyrin becomes maximum at a wavelength of about 390 nm, and gradually decreases as the wavelength becomes smaller or larger.

  As can be seen from this graph, by irradiating the subject with laser light having a central wavelength of 405 nm as excitation light for autofluorescence observation, the porphyrin in the observation region is mainly excited to generate autofluorescence. it can. In addition, by irradiating a subject with laser light having a central wavelength of 445 nm as excitation light for autofluorescence observation, FAD in the observation region can be mainly excited to generate autofluorescence.

  Next, FIG. 5 is an example graph showing the fluorescence intensity characteristics of the autofluorescent material. In the figure, the vertical axis represents the fluorescence intensity (a.u.) of the autofluorescent material, and the horizontal axis represents the wavelength (nm). This graph corresponds to the graph shown in FIG. 4. When the laser light having a central wavelength of 405 nm is irradiated as the excitation light for autofluorescence observation onto the subject's observation area, the normal part and the lesion part are shown. It shows the fluorescence intensity distribution of autofluorescence emitted from the autofluorescent material.

  When the subject is irradiated with laser light having a central wavelength of 405 nm as excitation light for autofluorescence observation, the porphyrin is mainly excited as described above, and the observation region irradiated with the excitation light as shown in FIG. Autofluorescence in the wavelength range of about 480-740 nm.

  The fluorescence intensity of the lesion part gradually increases as the wavelength increases from about 480 nm, reaches the first maximum at a wavelength of about 560 nm, then decreases gradually as the wavelength increases, and reaches a minimum at a wavelength of about 610 nm. The fluorescence intensity gradually increases again as the wavelength increases from about 610 nm, reaches the second maximum at the wavelength of about 630 nm, and then gradually decreases as the wavelength increases. The vicinity of the second maximum is fluorescence emitted mainly from porphyrin.

  On the other hand, the fluorescence intensity of the normal part gradually increases as the wavelength increases from about 480 nm, reaches a maximum at a wavelength of about 550 nm, and then gradually decreases as the wavelength increases.

  It is known that porphyrin accumulates in the lesioned part, and as shown in the graph of FIG. 5, the fluorescence intensity of porphyrin is stronger in the lesioned part than in the normal part. Therefore, it is possible to distinguish the normal part from the lesioned part by grasping the difference in the fluorescence intensity of porphyrin (reference: Mamoru Tamura, “Series / Life Science Opened by Light, Volume 6 Medical Diagnosis by Light”) , Japan Photobiology Association, Kyoritsu Shuppan, March 18, 2001).

  Further, the graph shown in FIG. 6 is emitted from autofluorescent substances in the normal part and the lesion part when laser light having a central wavelength of 445 nm is irradiated to the subject's observation area as excitation light for autofluorescence observation. The fluorescence intensity distribution of autofluorescence is shown.

  When the subject is irradiated with laser light having a central wavelength of 445 nm as excitation light for autofluorescence observation, the FAD is mainly excited as described above, and the observation subject is irradiated with excitation light as shown in FIG. Autofluorescence is emitted in the wavelength range of about 480 to 720 nm from the region.

  The fluorescence intensity of the lesioned part and the normal part gradually increases as the wavelength increases from about 480 nm, reaches a maximum at a wavelength of about 550 nm, and then gradually decreases as the wavelength increases. The vicinity of the maximum is the fluorescence emitted mainly from the FAD.

  As shown in the graph of FIG. 6, the fluorescence intensity of FAD is weaker in the lesion than in the normal part. Therefore, it is possible to distinguish between a normal part and a lesion part in the same manner by grasping the difference in the fluorescence intensity of FAD.

Subsequently, FIG. 7 is a graph showing the extinction coefficients of oxygenated hemoglobin and reduced hemoglobin. The vertical axis of this graph represents the hemoglobin extinction coefficient μa (cm −1 ), and the horizontal axis represents the wavelength (nm). As shown in this graph, blood hemoglobin has a light absorption characteristic in which the light absorption coefficient μa changes depending on the wavelength of light to be irradiated. The extinction coefficient μa represents absorbance, which is the magnitude of light absorption of hemoglobin. Further, reduced hemoglobin Hb that is not bonded to oxygen and oxidized hemoglobin HbO 2 that is bonded to oxygen have different light absorption characteristics and have the same absorbance (absorption coefficient μa) (the same as the reduced hemoglobin in FIG. 7). Except for the point of intersection with oxyhemoglobin), there is a difference in absorbance. In general, since the distribution of FIG. 7 changes nonlinearly depending on the region to be imaged, it is necessary to obtain in advance by actual measurement of biological tissue, light propagation simulation, or the like.

  FIG. 8 is an example graph showing the fluorescence intensity characteristics of FAD with and without blood. This graph shows the fluorescence intensity distribution of the autofluorescence emitted from the normal part autofluorescent material shown in FIG. 6, that is, mainly from the FAD. From the graph of FIG. 7, there is a light absorption peak due to blood in the vicinity of a wavelength of 550 nm. From the graphs of FIGS. 5 and 6, the maximum fluorescence wavelength of FAD is about 550 nm, which matches the absorption peak wavelength of hemoglobin. Therefore, as shown in the graph of FIG. 8, when a blood vessel is present above the position where the FAD is present in the living tissue, the fluorescence spectrum of the FAD has a fluorescence intensity corresponding to the absorption of light by the blood. Is attenuated.

  In order to eliminate the influence of light absorption by blood, the amount of light absorbed by blood can be obtained from the reflectance (signal intensity) of the reflected light image in the same wavelength region as the emission wavelength of autofluorescence. However, the relationship between the fluorescence intensity and the reflectance is not simply a linear relationship because the propagation lengths of autofluorescence and reflected light in living tissue are different. That is, the reflected light sees the light itself incident on the living tissue, that is, the light incident on the living tissue is scattered inside the living tissue and comes out of the living tissue again. Autofluorescence, on the other hand, scatters light that has entered the living tissue, and is only generated when it reaches the autofluorescent material. The autofluorescence generated at that position scatters within the living tissue. , Watching what has come out of the living tissue.

  FIG. 9 is a graph showing an example of the relationship between reflectance and fluorescence intensity and blood concentration. The vertical axis of this graph is the normalized signal intensity (a.u.) of reflectance (reflected light) and fluorescence intensity (autofluorescence), and the horizontal axis is blood concentration. The graph shown in the figure is normalized so that both the autofluorescence and the signal intensity of reflected light are 1 when the blood concentration is 0. From this graph, it can be seen that when light encounters a region where blood such as blood vessels exists in the process of light scattering in the living tissue, the signal intensity of the light decreases due to the influence of light absorption by the blood. In particular, as the blood concentration increases, the signal intensity (reflectance) of reflected light decreases more than the signal intensity (fluorescence intensity) of autofluorescence. As described above, since the reflected light generally has a longer distance to scatter in the living tissue, it has a characteristic that it is more susceptible to light absorption by blood than autofluorescence.

  FIG. 10 is an example of a graph showing the relationship between the fluorescence intensity and the reflectance. The vertical axis of this graph is the fluorescence intensity (a.u.), and the horizontal axis is the reflectance (a.u.). As indicated by the dotted line in this graph, if the distance at which the autofluorescence and the reflected light scatter within the living tissue is the same, the fluorescence intensity and the reflectance have a linear relationship. However, as described above, since the reflected light generally has a longer distance to scatter in the living tissue than the autofluorescence, as shown by the solid line in this graph, the two have a non-linear relationship. The non-linearity increases at the portion where the density of the light is high and the reflectance is low.

  FIG. 11 is an exemplary graph showing a correction coefficient for correcting the fluorescence intensity of autofluorescence. The vertical axis of this graph is the correction coefficient, and the horizontal axis is the reflectance (a.u.). As indicated by the dotted line in this graph, if the fluorescence intensity and the reflectance are in a linear relationship, the correction coefficient is a constant value regardless of the reflectance. However, as shown by the solid line in this graph, the relationship between the two is non-linear. In particular, since the non-linearity is large in the portion where the reflectance is low, the correction coefficient in the portion where the reflectance is low is compared with the portion where the reflectance is high. Is set to be large. In this way, by correcting the fluorescence intensity corresponding to the reflectance with the correction coefficient corresponding to the reflectance, the nonlinearity between the two is corrected, and from the autofluorescence image, the absorption of light by blood is corrected. The influence can be eliminated.

  The correction coefficient shown in FIG. 11 can be experimentally calculated in advance. For example, in a container such as a petri dish, a scattering substance (a solution having the same scattering characteristics as a living body, for example, an intralipid solution 1%) and a fluorescent substance (FAD, porphyrin (concentration is about 10 μmol close to the concentration in a living tissue). )) And reflected light imaging and autofluorescence imaging are performed while changing the blood concentration (hemoglobin concentration) in the range of 0 to 300 mg / dl. Then, the graph of FIG. 10 is created for the image signal of the G channel in the same wavelength range as the emission wavelength of the FAD and the R channel in the same wavelength range as the emission wavelength of the porphyrin, so that the fluorescence intensity becomes a certain value. The correction coefficient shown in FIG. 11 can be generated for the G channel and R channel image signals from the amount of deviation from 10 linear lines.

  The correction coefficient table storing the relationship between the reflectance of the reflected light image and the correction coefficient may be used to obtain a correction coefficient corresponding to the reflectance of the reflected light image, or instead of the correction coefficient table. Alternatively, a correction coefficient calculation function or the like may be used.

  Next, FIGS. 12 and 13 show the spectral transmission characteristics of the color filters provided on the light receiving surface of the image sensor 58B in the graphs of FIGS. 5 and 6, respectively. The spectral transmittance (%) of the color filter is shown on the vertical axis on the right side of the figure. These graphs also show the center wavelengths 405 nm and 445 nm of laser light used as excitation light for autofluorescence observation, respectively.

  As shown in these graphs, the G color filter is designed to transmit light in a wavelength range of 500 to 620 nm centered around a wavelength of 550 nm. As a result, autofluorescence mainly emitted from the FAD passes through the G color filter and is photoelectrically converted by the image sensor 58B. The R color filter is designed to transmit light in the wavelength range of 580 to 700 nm centered around the wavelength of 630 nm. Thereby, autofluorescence mainly emitted from porphyrin passes through the R color filter and is photoelectrically converted by the image sensor 58B.

  The G color filter transmits light in the wavelength range of 500 nm to 600 nm, and the R color filter transmits light in the wavelength range of 600 nm to 700 nm. It is desirable to be.

  As described above, the image sensor 58B is not provided with a B color filter. That is, the laser light having the center wavelengths of 405 nm and 445 nm, which is the excitation light for autofluorescence observation, is cut so that it is not photoelectrically converted by the image sensor 58B.

  Subsequently, FIG. 14 is a graph showing the fluorescence intensity distribution of the autofluorescence when the laser light having the central wavelengths of 405 nm and 445 nm is simultaneously irradiated as excitation light for autofluorescence observation, and the spectral transmission characteristics of the color filter are superimposed and displayed. It is a thing. The figure also shows the central wavelengths of 405 nm and 445 nm of laser light used as excitation light for autofluorescence observation.

  As shown in this graph, when laser light with central wavelengths of 405 nm and 445 nm is simultaneously irradiated as excitation light for autofluorescence observation, the fluorescence intensity of autofluorescence in the lesioned part and the normal part is mainly around the wavelength of 550 nm. It can be seen that there is a large difference between autofluorescence emitted from FAD and autofluorescence emitted mainly from porphyrin near the wavelength of 630 nm.

  Accordingly, the autofluorescence is dispersed with the G color filter and the R color filter to obtain the G autofluorescence image and the R autofluorescence image, respectively. And the difference in fluorescence intensity between lesions. Similarly, in the R-color autofluorescence image, the difference in fluorescence intensity between the normal part and the lesion part due to porphyrin can be captured.

FIG. 15 is a graph showing an example of the relationship between the blood absorption coefficient and the color filter in the normal sensor. The vertical axis of this graph represents the hemoglobin extinction coefficient μa (cm −1 ), and the horizontal axis represents the wavelength (nm). As shown in this graph, the wavelength characteristics of the G color filter and the R color filter in the normal sensor are the same as those shown in FIG. 14, and from the G signal and R color image signals (image data) of the normal sensor. It can be seen that information on light absorption by blood corresponding to the wavelengths of G and R can be obtained.

  Next, the operation of the endoscope diagnosis apparatus 10 will be described with reference to the conceptual diagrams shown in FIGS.

  In the normal light observation mode, under the control of the light source control unit 22, the laser light source LD1 is turned off and the laser light source LD2 is turned on. Laser light having a central wavelength of 445 nm emitted from the laser light source LD2 is applied to the phosphors 54A and 54B, and white light is emitted from the phosphors 54A and 54B. As shown in FIG. 16, the white light emitted from the phosphors 54A and 54B is irradiated to the subject, and the reflected light is received by the image sensor 58A (normal sensor), and images of the R, G, and B channels are obtained. A normal light image including the signal is captured. The normal light image is displayed in color based on the B, G, and R channel image signals (normal light image processing).

  In the case of the auto fluorescence observation mode, as shown in FIG. 17, for example, imaging is repeatedly performed in units of 2 frames. Of the two frames, the first frame is the same observation mode as the normal light observation mode, and the second frame is an observation mode unique to the autofluorescence observation mode.

  First, in the normal light observation mode of the first frame, as described above, a normal light image including R, G, and B channel image signals is captured. Then, the normal light image signal is stored in the storage unit 72 under the control of the control unit 68.

  Subsequently, in the auto-fluorescence observation mode of the second frame, as shown in FIG. 17, both the laser light sources LD1 and LD2 are turned on under the control of the light source control unit 22. As shown in FIG. 16, a laser beam having a central wavelength of 405 nm (excitation light 1) emitted from the laser light source LD1 and a laser beam having a central wavelength of 445 nm (excitation light 2) emitted from the laser light source LD2 Are simultaneously irradiated, the autofluorescence emitted from the subject is received by the image sensor 58B (high sensitivity sensor), and an autofluorescence image including R and G channel image signals is captured. Then, the autofluorescence image signal is stored in the storage unit 72 under the control of the control unit 68.

  As described above, the image sensor 58B is not provided with the B color filter, but only the G and R color filters. Therefore, the excitation light having the center wavelengths of 405 nm and 445 nm, which is the wavelength range of B color, is cut, and autofluorescence in the wavelength range of 500 nm to 700 nm, which is the wavelength range of G color and R color, is received by the image sensor 58B. Can do.

  Subsequently, in the autofluorescence image processing unit 70B, using the normal light image signal and the autofluorescence image signal stored in the storage unit 72, for example, from the correction coefficient table in the graph relationship shown in FIG. Correction coefficients corresponding to each of the R and G channel image signals (reflectance) of the image (reflected light image) are obtained, and the signal intensity of the R and G channels of the autofluorescence image is determined using the obtained correction coefficient. Each is corrected. This eliminates the influence of light absorption by blood in the R and G channel image signals of the autofluorescence image. Here, R ′ and G ′ are the R and G channel image signals of the corrected autofluorescence image.

  Then, the normal light image corresponding to the normal light image signal stored in the storage unit 72 and the corrected autofluorescence image are combined and the combined image of both is displayed on the display device 18. Here, the auto-fluorescent image is controlled by the control unit 68 by assigning the G-color image signal G ′ of the corrected auto-fluorescence image to the G channel and the R-color image signal R ′ to the R channel and the B channel. A pseudo color is displayed on the display device 18 (autofluorescence image processing).

  As shown in FIG. 18, in the normal part, the fluorescence intensity of FAD is strong, while the fluorescence intensity of porphyrin is weak, and in the lesion part, the reverse relationship is obtained. Further, as described above, the endoscope diagnosis apparatus 10 performs pseudo color display by assigning the G channel image signal to the G channel and the R channel image signal to the R channel and the B channel. For this reason, the autofluorescence image displayed in pseudo color by the endoscope diagnostic apparatus 10 is represented by a normal part in green and a lesion part in magenta. The contrast of the lesion is stronger than that of the autofluorescence image, and the lesion is easily recognized.

  As described above, the endoscope diagnostic apparatus 10 corrects the signal intensity of the autofluorescence image using the correction coefficient corresponding to the reflectance of the reflected light image in the same wavelength range as the emission wavelength range of the autofluorescence. An autofluorescence image that is not affected by light absorption by blood can be obtained.

  In the case of the autofluorescence observation mode, it is not essential to repeat imaging in units of 2 frames. In the auto-fluorescence observation mode, it is not essential to simultaneously irradiate the laser beam having the center wavelength of 405 nm and the laser beam having the center wavelength of 445 nm. For example, even if these laser beams are sequentially irradiated for each frame. Good. In addition, when pseudo-color display is performed on the autofluorescence image, it is arbitrary which image signal of which color channel is assigned to which color channel. Further, the autofluorescent substance is not limited to porphyrin and FAD.

The present invention is basically as described above.
Although the present invention has been described in detail above, the present invention is not limited to the above-described embodiment, and it is needless to say that various improvements and modifications may be made without departing from the gist of the present invention.

DESCRIPTION OF SYMBOLS 10 Endoscope diagnostic apparatus 12 Light source apparatus 14 Endoscope apparatus 16 Processor apparatus 18 Display apparatus 20 Input apparatus 22 Light source control part 24 Combiner 26 Coupler 28 Endoscope insertion part 30 Operation part 32A, 32B Connector part 34 Flexible part 36 Curve Part 38 Tip 40 Angle knob 42A, 42B Illumination window 44 Observation window 45 Forceps port 46A, 46B, 48A, 48B Optical fiber 50A, 50B, 52A, 52B, 56 Lens 54A, 54B Phosphor 57 Half mirror 58A, 58B Imaging element 62A, 62B Scope cable 64A, 64B A / D converter 66 Changeover switch 68 Control unit 70 Image processing unit 70A Normal light image processing unit 70B Autofluorescence image processing unit 72 Storage unit LD1, LD2 Laser light source

Claims (14)

  1. A light source unit that emits one or more first excitation lights having different center wavelengths for emitting white light and one or more autofluorescences from a plurality of autofluorescent substances included in the observation region of the subject;
    When the white light is irradiated from the light source unit onto the subject's observation area, the reflected light image of the white light from the observation area of the subject is received and a reflected light image is captured; and When the first excitation light is irradiated from the light source unit to the observation area of the subject, the self-fluorescence emitted from the autofluorescent substance contained in the observation area of the subject is received An imaging unit that captures a fluorescent image;
    Correction coefficient for correcting that autofluorescence emitted from the autofluorescent material contained in the subject's observation region is absorbed by blood and that the signal intensity of the autofluorescence image is reduced according to the amount of blood A correction coefficient corresponding to the reflectance of the reflected light image is determined from the correction coefficient, the signal intensity of the autofluorescence image is corrected using the calculated correction coefficient , and the white light is A first propagation length until the imaging region receives the reflected light of the white light from the observation region of the subject and the white light reflected from the observation region of the subject, and the first excitation light Depending on the difference in the second propagation length until the imaging unit receives the autofluorescence emitted from the autofluorescent material included in the subject's observation area. The reflectance of the reflected light image and the signal intensity of the autofluorescence image Endoscopic diagnosis apparatus characterized by comprising an image correcting unit for correcting the non-linearity occurring.
  2. The image correction unit has a correction coefficient table in which the relationship between the reflectance of the reflected light image and the correction coefficient is stored, and using the correction coefficient table, a correction coefficient corresponding to the reflectance of the reflected light image The endoscope diagnosis apparatus according to claim 1 , wherein:
  3. The light source unit, the a first excitation light, endoscopic diagnosis apparatus according to claim 1 or 2 in which emits excitation light of at least one of the predetermined wavelength range having a center wavelength of 405nm and 445 nm.
  4. The endoscope diagnosis apparatus according to claim 3 , wherein the light source unit includes a laser light source that emits the first excitation light.
  5. The light source unit is irradiated with a white light source that emits second excitation light in a predetermined wavelength range having a center wavelength of 445 nm, and a second excitation light emitted from the white light source, so that the predetermined light source includes the second excitation light. endoscopic diagnosis apparatus according to any one of claims 1-4 in which and a phosphor that emits pseudo white light in the wavelength range.
  6. The endoscope diagnosis apparatus according to claim 5 , wherein the light source unit includes a laser light source that emits the second excitation light.
  7. The imaging unit includes an imaging element that captures the reflected light image and the autofluorescence image, and a wavelength that is disposed on an optical path of the imaging element and has a spectral transmission characteristic that transmits light in a wavelength range corresponding to green and red endoscopic diagnosis apparatus according to any one of claims 1 to 6 in which and a selection member.
  8. The endoscope diagnosis apparatus according to claim 7 , wherein the wavelength selection member is a color filter.
  9. The endoscope diagnosis apparatus according to claim 7 , wherein the wavelength selection member is an etalon, the green wavelength range is 500 to 600 nm, and the red wavelength range is 610 to 650 nm.
  10. The imaging unit has a first imaging element that captures the reflected light image, and a spectral transmission characteristic that is disposed on an optical path of the first imaging element and transmits light in a wavelength range corresponding to blue, green, and red. A first wavelength selection member, a second image sensor that is more sensitive than the first image sensor that captures the autofluorescence image, and a wavelength range that is disposed on the optical path of the second image sensor and corresponds to green and red endoscopic diagnosis apparatus according to any one of claims 1 to 6 in which and a second wavelength selective member having a spectral transmission characteristic of transmitting the light.
  11. The endoscope diagnosis apparatus according to claim 10 , wherein the first and second wavelength selection members are color filters.
  12. The endoscope diagnostic apparatus according to claim 10 , wherein the first and second wavelength selection members are etalon, the green wavelength range is 500 to 600 nm, and the red wavelength range is 610 to 650 nm.
  13. The said image correction | amendment part correct | amends the signal strength of the green and red image signal of the said autofluorescence image based on the reflectance of the green and red image signal of the said reflected light image, respectively. endoscopic diagnosis apparatus according to any one of 12.
  14. The endoscopic diagnosis apparatus according to claim 13 , further comprising: a display device that performs pseudo color display by assigning a green image signal of the corrected autofluorescence image to a green channel and a red image signal to a red channel and a blue channel. .
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