JP2014046075A - Optical unit, and endoscope device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an optical unit and an endoscope device capable of easily imaging an observation object part and performing spectrometry for a measurement object part with one image pick-up element.SOLUTION: An optical unit 135 includes: an image pick-up element 150 where an imaging area 154 (a first photo detecting area) for receiving imaging light of an observation object part and a spectral area 152 (a second photo detecting area) for receiving radiation light of a measurement object part are formed on the same photo detecting surface; an imaging optical system 180 for guiding imaging light to the imaging area 154; a spectral optical system 160 for guiding radiation light to the spectral area 152; and a casing 190 for storing the imaging optical system 180 and the spectral optical system 160 in parallel to the observation object part. A shading mask 182 having an opening 182a for limiting the area of a passing light beam is disposed on an optical path of the imaging optical system 180.

Description

  The present invention relates to an optical unit and an endoscope apparatus.

  In addition to imaging the site to be observed in the body lumen, the spectrum data is acquired by spectrally analyzing the autofluorescence, which is the emitted light emitted from the site to be measured by irradiating the site to be measured with excitation light. 2. Description of the Related Art Endoscopic apparatuses capable of performing spectroscopic measurement of a part are known.

  In such an endoscope apparatus, for example, Patent Document 1 discloses that an imaging element (for example, a CCD (Charge Coupled Device)) used for imaging an observation target region is also used for spectroscopic measurement of the measurement target region.

  In the endoscope apparatus described in Patent Document 1, the light receiving surface of the imaging element is divided into two areas for imaging and spectroscopic measurement. And the filter comprised so that the fluorescence of a different wavelength may inject into each sub area | region which comprises the area | region for spectroscopic measurement is arrange | positioned covering the area | region for spectroscopic measurement. This spectral filter (hereinafter referred to as “spectral filter”) is divided into a plurality of microscopic areas in a staggered pattern in accordance with individual sub-regions. For example, 350 ± 2.5 [nm] light is transmitted in an area corresponding to a certain sub-region, and 355 ± 2.5 [nm] light is transmitted in an area corresponding to the adjacent sub-region. As described above, this spectral filter separates fluorescence having a wavelength band of a certain width in increments of 5 [nm], and separates fluorescence of each divided wavelength band into separate sub-regions in a spectral measurement region provided in the image sensor. Incident into the area.

JP 2005-185513 A

  In the technique described in Patent Document 1, in order to obtain (spread) the intensity for a specific wavelength of autofluorescence, a bandpass filter for each wavelength region that is finely divided is directly pasted on the image sensor, and each bandpass From the fluorescence intensity obtained through the filter, the fluorescence intensity for each wavelength region, that is, the spectral distribution was obtained. However, it is very difficult to manufacture a bandpass filter whose wavelength region is finely divided. Even if it can be manufactured, it is technically very difficult to mount each bandpass filter on a pixel on an image sensor corresponding to each wavelength region. Moreover, in the electronic endoscope apparatus described in Patent Document 1, a single lens is shared for measurement and imaging, and a measurement region arranged in order in the longitudinal direction of the endoscope by a beam splitter and a total reflection mirror; Measurement light and imaging light are made incident on the imaging region, respectively. However, if fluorescence is guided to the measurement region using a beam splitter, the amount of fluorescence is easily lost, which is disadvantageous for measurement of weak fluorescence. In addition, it is difficult to produce a beam splitter having the performance of reflecting only fluorescence of a specific wavelength and transmitting light of other wavelength ranges, which tends to increase the cost. Furthermore, there is a possibility that a part of the fluorescence passes through the beam splitter and is reflected by the total reflection mirror and then enters the measurement area instead of the imaging area.

  An object of the present invention is to provide an optical unit and an endoscope apparatus that can solve the above-described problems of the prior art and that can easily perform imaging of a region to be observed and spectroscopic measurement of a region to be measured with a single image sensor. With the goal.

The optical unit according to the present invention is
An optical unit that receives imaging light of an observation target part of a body lumen and radiation light of a measurement target part of the body lumen,
A first light receiving region for receiving imaging light of the observation target region, and a second light receiving region for receiving radiation light of the measurement target region formed on the same light receiving surface;
An imaging optical system for guiding the imaging light to the first light receiving region;
A spectroscopic optical system for guiding the emitted light to the second light receiving region;
A housing that houses the imaging optical system and the spectroscopic optical system in parallel with the observation target part;
With
On the optical path of the imaging optical system, a light shielding mask having an opening for limiting the area of the light beam passing therethrough is disposed.
An endoscope apparatus according to the present invention includes:
An endoscope body having the optical unit;
Connected to the endoscope main body, processes imaging data of the observation target part imaged in the first light receiving region, and processes spectroscopic measurement data of the measurement target part spectroscopically measured in the second light receiving region An endoscope processor;
Is provided.

  According to the present invention, it is possible to provide an optical unit and an endoscope apparatus that can easily perform imaging of a site to be observed and spectroscopic measurement of a site to be measured with a single imaging device.

It is a figure which shows the structure of the endoscope apparatus in this Embodiment. It is a figure which shows the structure of the front-end | tip part of the insertion part in this Embodiment. It is a figure which shows the internal structure of the insertion part in this Embodiment. It is a flowchart which shows the imaging and spectroscopic measurement operation | movement in this Embodiment.

Hereinafter, the present embodiment will be described in detail with reference to the drawings.
[Configuration of Endoscope Device 10]
An endoscope apparatus 10 shown in FIG. 1 includes an endoscope main body 100 and an endoscope processor 200. The endoscope body 100 includes a flexible long insertion portion 110 formed so as to be introduced into a body lumen, an operation portion 120 provided at a proximal end portion 110a of the insertion portion 110, and an operation portion 120. And a cable 130 for connecting the insertion unit 110 and the endoscope processor 200 so as to communicate with each other.

  The insertion portion 110 has flexibility that can be easily bent according to the curvature of the lumen when entering the lumen, over substantially the entire length of the insertion portion 110. In addition, the insertion unit 110 has a mechanism (not shown) that can bend a certain range (operable unit 110c) on the distal end 110b side at an arbitrary angle in accordance with the operation of the knob 120a of the operation unit 120.

  As shown in FIG. 2, a first illumination window 111, a second illumination window 112, a first observation window 113, a second observation window 114, and a forceps channel 115 are disposed at the distal end portion 110b of the insertion portion 110. .

  The 1st illumination window 111 is an objective lens, for example, and irradiates the observation object site | part of a body lumen with the illumination light guided from the endoscope processor 200. FIG. The second illumination window 112 is, for example, an objective lens, and irradiates the measurement target site in the body lumen with the excitation light guided from the endoscope processor 200.

  The first observation window 113 captures reflected light from the observation target part as imaging light when the observation target part is irradiated with illumination light from the first illumination window 111. The first observation window 113 is an objective optical system including, for example, one objective lens or a plurality of lenses. The second observation window 114 is radiated light emitted from the measurement target part as a result of irradiating the reflected light and the excitation light from the measurement target part when the measurement target part is irradiated from the second illumination window 112. A certain autofluorescence is taken in as received light. The second observation window 114 is, for example, an objective optical system including one objective lens or a plurality of lenses.

  The forceps channel 115 is a lumen formed in the insertion portion 110 so as to communicate with the introduction port 120 b formed in the operation portion 120. Various devices for observing a lesion, diagnosing the lesion, performing surgery on the lesion, and the like can be inserted into the forceps channel 115.

[Internal Configuration of Insertion Unit 110]
Next, the internal configuration of the insertion section 110 will be described with reference to FIGS. FIG. 3B is a diagram schematically showing the main components (the spectroscopic optical system 160, the imaging optical system 180, and the imaging element 150) provided inside the insertion unit 110.

  The insertion unit 110 includes a first illumination window 111, a second illumination window 112, a forceps channel 115, an illumination optical fiber 140, an excitation optical fiber 142, and an optical unit 135.

  The illumination optical fiber 140 is a single optical fiber or a bundle of a plurality of optical fibers housed in the insertion unit 110, and guides the illumination light generated in the endoscope processor 200 to the vicinity of the distal end portion 110b of the insertion unit 110. Shine. Since the end face of the illumination optical fiber 140 is disposed to face the first illumination window 111, the illumination light emitted from the illumination optical fiber 140 is irradiated to the observation target site in the body lumen via the first illumination window 111. The

  The excitation optical fiber 142 is a single optical fiber or a bundle of a plurality of optical fibers housed in the insertion unit 110, and guides the excitation light generated in the endoscope processor 200 to the vicinity of the distal end 110b of the insertion unit 110. Shine. Since the end surface of the excitation optical fiber 142 is disposed to face the second illumination window 112, the excitation light emitted from the excitation optical fiber 142 is irradiated to the measurement target site in the body lumen via the second illumination window 112. The

  Light from the observation target part or measurement target part when illumination light or excitation light is irradiated to the observation target part or measurement target part passes through the optical unit 135 and is received by the insertion unit 110.

  The optical unit 135 includes an imaging device 150 including a complementary metal oxide semiconductor (CCD) or CMOS (Complementary Metal Oxide Semiconductor) image sensor, a spectral optical system 160, an imaging optical system 180, the spectral optical system 160, and the imaging optical system 180 with respect to an observation target region. For example, a resinous housing 190 is provided so as to be accommodated in parallel.

  The spectroscopic optical system 160 splits the autofluorescence emitted from the measurement target site by the irradiation of the excitation light and guides it to the spectral region 152 (second light receiving region) of the image sensor 150.

  The imaging optical system 180 guides imaging light emitted from the observation target site to the imaging area 154 (first light receiving area) of the imaging element 150 by irradiation of illumination light.

  The spectroscopic optical system 160 includes a second observation window 114, a band pass filter 162, a slit 164, a collimator lens 166, a diffraction grating 168, and a condenser lens 170.

  The second observation window 114 collects the received light (reflected excitation light and autofluorescence) emitted from the measurement target site by irradiation with excitation light.

  The bandpass filter 162 is an optical filter having a characteristic of transmitting only light of a specific wavelength and reflecting other light. By providing such a filter, unnecessary light components can be removed. In the present embodiment, the band pass filter 162 transmits only the autofluorescence to be measured among the received light collected by the second observation window 114.

  The slit 164 is formed in a rectangular shape and adjusts the width of light incident on the diffraction grating 168.

  The collimator lens 166 converts the light beam from the slit 164 into a substantially parallel light beam.

  The diffraction grating 168 is a transmission type diffraction grating, and decomposes (splits) the light that has passed through the collimating lens 166 into each wavelength and emits the light toward the condenser lens 170.

  The condensing lens 170 condenses the light of each wavelength separated by the diffraction grating 168 and emits it to the spectral region 152 of the image sensor 150.

  The imaging optical system 180 includes a first observation window 113, a light shielding mask 182, and a condenser lens 184.

  The 1st observation window 113 condenses the imaging light emitted from an observation object site | part by irradiation of illumination light.

  The light shielding mask 182 is a frame made of an opaque material such as black, and is disposed, for example, at the focal position of the first observation window 113 on the optical path of the imaging optical system 180. The light shielding mask 182 is provided with a quadrangular opening 182a that limits the area of the light beam passing therethrough. As shown in FIG. 3B, the area of the opening 182a includes the shape and focal position of the lens (the first observation window 113, the condensing lens 184), the tolerance in manufacturing the lens, the assembly tolerance of the imaging optical system 180, and the like. In consideration, the range in which the light that has passed through the condenser lens 184 reaches (light ray arrival area A) is designed not to reach the spectral area 152 of the image sensor 150. The shape of the opening 182a may be an arbitrary shape such as a circular shape or a polygonal shape other than a quadrangle. In short, any shape that can prevent light incident on the imaging optical system 180 from reaching the spectral region 152 may be used.

  The condenser lens 184 condenses the imaging light that has passed through the light shielding mask 182 and emits it to the imaging region 154 of the imaging device 150.

  In the present embodiment, the imaging optical system 180 and the spectroscopic optical system 160 are arranged in parallel to the observation target part, and each guides light independently, so that an optical separation element such as a beam splitter is used. The light can be guided to the image sensor 150 without going through. Therefore, the loss of the radiated light emitted from the measurement site is avoided by the beam splitter, which is advantageous for measuring weak fluorescence. In addition, an optical separation element such as a beam splitter is unnecessary, the configuration is simplified, and an increase in cost can be suppressed. In this embodiment, the diffraction grating 168 that performs spectroscopy is a transmissive type, but may be a reflective type. Further, a prism may be used instead of the diffraction grating 168 as an optical element for performing spectroscopy. Further, as an optical element for adjusting the light width, a pinhole may be used instead of the slit 164.

  The imaging element 150 is a monochrome type that is provided on the circuit board 156 and has no color filter provided on each pixel in the spectral region 152 and the imaging region 154. In the imaging element 150, a rectangular spectral region 152 and an imaging region 154 are formed on the same light receiving surface. The imaging element 150 is arranged so that both the imaging light that has passed through the imaging optical system 180 and the autofluorescence that has passed through the spectroscopic optical system 160 enter the light receiving surface 150a and form an image on the light receiving surface 150a. Yes. The imaging element 150 obtains an electrical signal representing image information and measurement information by photoelectrically converting the imaged light. The generated electrical signal is transmitted into the endoscope processor 200.

Here, the imaging light that has passed through the imaging optical system 180 enters the imaging region 154 provided on the light receiving surface 150a without being split. Therefore, an image signal (hereinafter referred to as “imaging signal”) obtained from the imaging light incident on the imaging region 154 represents an image of the observation target region irradiated with the illumination light, and an image or video of the observation target region. Can be used for display. On the other hand, the autofluorescence that has passed through the spectroscopic optical system 160 is split and imaged at different positions for each wavelength component in the spectral region 152 provided on the light receiving surface 150a. That is, each pixel constituting the spectral region 152 can detect autofluorescence as the intensity for each wavelength component. Therefore, a measurement signal obtained from autofluorescence incident on the spectral region 152 (hereinafter referred to as “spectral measurement signal”) represents an autofluorescence spectrum, and is used to acquire autofluorescence spectrum data from a measurement target site. be able to.
As described later, broadband wavelength light such as white light is used as illumination light for imaging. If the illumination light for imaging is incident upon the measurement of autofluorescence, the illumination light is turned off during measurement because accurate measurement cannot be performed. When the excitation light is irradiated with the illumination light turned off, the emitted light (in this case, autofluorescence) enters not only the spectroscopic optical system 160 but also the imaging optical system 180. If radiated light incident on the imaging optical system 180 enters the spectral region 152, the measurement data may become inaccurate. In order to prevent this, it is conceivable to provide a shutter on the front end side of the imaging optical system 180, but this leads to an increase in cost and complexity and size of the configuration. Therefore, in the present embodiment, a shutter is provided on the front side of the imaging optical system 180 by disposing a light-shielding mask 182 having an opening for limiting the area of the light beam passing through on the optical path of the imaging optical system 180. In this way, the radiated light incident on the imaging optical system 180 is prevented from entering the spectral region 152.

  Note that the imaging region 154 is desirably as wide as possible as compared to the spectral region 152, and the number of pixels constituting the spectral region 152 may be at least one line. However, when the intensity of the autofluorescence that is the target of the spectroscopic measurement is weak, it is desirable to increase the sensitivity of the entire spectroscopic region 152 by increasing the number of lines of pixels that constitute the spectroscopic region 152.

[Configuration of Endoscope Processor 200]
Next, the configuration of the endoscope processor 200 will be described. The endoscope processor 200 includes a control unit 210, a memory 212, a light source unit 220, a spectral analysis unit 230, and an image processing unit 240. An input device 300 and a monitor 400 are connected to the endoscope processor 200.

  The input device 300 inputs a user instruction to the endoscope processor 200. In the present embodiment, the input device 300 includes, for example, a keyboard, a mouse, a switch, or the like. The monitor 400 is a liquid crystal display, for example, and displays various images by inputting the image data output from the endoscope processor 200.

  The control unit 210 controls the operation of each block of the endoscope processor 200.

  The light source unit 220 includes an illumination light source 222 and an excitation light source 224. The illumination light source 222 is an illumination for observation when an instruction to execute an image capturing mode for illuminating a site to be observed and observed in the body lumen (for example, a lesioned part) is input to the input device 300 after the endoscope processor 200 is activated. Emits light. As the illumination light source 220, one that generates broadband light such as white light is used. When the insertion portion 110 of the endoscope main body 100 is introduced into the body lumen, the insertion portion 110 guides the illumination light emitted from the illumination light source 222 and emits it to the observation target site.

  The excitation light source 224 emits a light source such as xenon light and emits a band-pass filter or the like when an instruction to execute a spectroscopic measurement mode for inspecting a measurement target site (for example, a lesion) in a body lumen is input to the input device 300. Thus, excitation light having a specific wavelength is obtained. When the insertion portion 110 of the endoscope main body 100 is introduced into the body lumen, the insertion portion 110 guides the excitation light emitted from the excitation light source 224 and emits the excitation light to the measurement target site.

  The spectroscopic analysis unit 230 analyzes the presence / absence and type of a lesion in the measurement target site of the body lumen based on the spectroscopic measurement signal transmitted from the insertion unit 110 (imaging device) of the endoscope body 100. Then, the control unit 210 causes the monitor 400 to display the analysis result image by outputting the analysis result image data indicating the analysis result to the monitor 400. The user can evaluate the extent of the lesion and the degree of illness by looking at the analysis result image displayed on the monitor 400.

  The memory 212 is a storage device such as an HDD (Hard Disk Drive) built in the endoscope processor 200. The memory 212 stores an analysis result by the control unit 210 and the like. Note that the memory 212 does not have to be built in the endoscope processor 200, for example, may be externally attached to the endoscope processor 200, or exists on a communication network. There may be.

  The image processing unit 240 receives an imaging signal from the insertion unit 110 (imaging element) of the endoscope body 100 and performs predetermined signal processing on the imaging signal. The control unit 210 outputs the processed signal to the monitor 400 as an endoscope video signal. Thus, when an observation target part of the body lumen is imaged, an endoscope image based on the endoscope image signal is displayed on the screen of the monitor 400.

[Imaging and Spectroscopic Measurement Operation in Endoscope Device 10]
Next, imaging and spectroscopic measurement operations in the endoscope apparatus 10 will be described with reference to the flowchart of FIG. Step S100 in FIG. 4 starts when an input instruction of an image capturing mode for illuminating the observation target region of the body lumen is input to the input device 300.

  First, the illumination light source 222 emits illumination light for observation (step S100). The illumination light emitted from the illumination light source 222 is emitted to the observation target site via the insertion unit 110 of the endoscope body 100. Next, the image processing unit 240 receives an imaging signal from the insertion unit 110 (imaging device) of the endoscope body 100, and performs predetermined signal processing on the imaging signal (step S120).

  Next, the control unit 210 outputs the processed signal to the monitor 400 as an endoscopic video signal, thereby displaying an endoscopic video based on the endoscopic video signal on the screen of the monitor 400 (step S140). ). Next, the control unit 210 determines whether or not an instruction to execute a spectroscopic measurement mode for inspecting a measurement target region of the body lumen is input to the input device 300 (step S160). As a result of this determination, when the execution instruction of the spectroscopic measurement mode is not input (step S160, NO), the process returns to before step S120.

  On the other hand, when the execution instruction for the spectroscopic measurement mode is input (step S160, YES), the illumination light source 222 ends the illumination light emission operation (step S180). Next, the excitation light source 224 emits excitation light (step S200). Excitation light emitted from the excitation light source 224 is emitted to the measurement target portion via the insertion portion 110 of the endoscope main body 100.

  Next, the spectroscopic analysis unit 230 analyzes the presence / absence and type of the lesion in the measurement target site in the lumen based on the spectroscopic measurement signal transmitted from the insertion unit 110 (imaging device) of the endoscope body 100 ( Step S220). Next, the control unit 210 causes the monitor 400 to display the analysis result image by outputting the analysis result image data indicating the analysis result to the monitor 400 (step S240).

  Next, the controller 210 determines whether or not a predetermined time (for example, several seconds) has elapsed after the excitation light is emitted in step S200 (step S260). As a result of this determination, when the predetermined time has not elapsed (step S260, NO), the process returns to before step S220.

  On the other hand, when the predetermined time has elapsed (step S260, YES), the excitation light source 224 ends the excitation light emission operation (step S280). Thereafter, the process returns to step S100, and the operation mode of the endoscope processor 200 transitions from the spectroscopic measurement mode to the image capturing mode.

[Effects of the present embodiment]
As described above in detail, the optical unit 135 in the present embodiment has the imaging region 154 (first light receiving region) that receives the imaging light of the observation target region, and the spectral region 152 (light receiving the autofluorescence of the measurement target region). An imaging element 150 having a second light receiving region) formed on the same light receiving surface, an imaging optical system 180 that guides imaging light to the imaging region 154, and a spectral optical system 160 that guides autofluorescence to the spectral region 152. A housing 190 that houses the imaging optical system 180 and the spectroscopic optical system 160 so as to be parallel to the site to be observed.

  According to the present embodiment configured as described above, the bandpass filter for each wavelength region that is finely divided is pasted on the image sensor 150 by using the spectroscopic optical system 160 as means for separating the autofluorescence. Thus, it is possible to acquire autofluorescence spectrum data from the measurement target site. Therefore, it is possible to easily perform imaging of the observation target region and spectroscopic measurement of the measurement target region with one image sensor 150.

  Further, according to the present embodiment, on the optical path of the imaging optical system 180, the light shielding mask 182 having the opening 182a that limits the area of the light beam passing therethrough is disposed. With this configuration, the range in which the light that has passed through the condenser lens 184 reaches (light ray arrival region) does not reach the spectral region 152 of the image sensor 150, and radiation emitted from the measurement target site when irradiated with excitation light. It can be prevented that part of the light enters the spectral region 152 via the imaging optical system 180 and adversely affects the spectral measurement of the measurement target region.

[Modification]
In the above embodiment, an example in which the image sensor 150 is a monochrome type has been described, but the present invention is not limited to this. For example, the image sensor 150 may be a color type in which a color filter (not shown) is pasted on the image area 154. However, in this case, it is preferable that the spectral region 152 grasps the light transmission characteristics of the color filter in advance and converts it so that the intensity of the emitted light becomes correct.

  In the above-described embodiment, the example in which the excitation light source 224 ends the emission operation of the excitation light when a predetermined time has elapsed after the emission of the excitation light has been described, but the present invention is not limited to this. For example, when the excitation light source 224 receives autofluorescence of a predetermined light amount or more in the spectral region 152 of the image sensor 150 after the excitation light is emitted, or the user inputs an instruction to end the spectroscopic measurement mode to the input device 300. In this case, the excitation light emission operation may be terminated.

  Moreover, although the insertion part 110 demonstrated the example which has the illumination optical fiber 140 and the excitation optical fiber 142 in the said embodiment, this invention is not limited to this. For example, the insertion unit 110 may include one optical fiber that functions as the illumination optical fiber 140 and the excitation optical fiber 142. In this case, a single illumination window that also functions as the first illumination window 111 and the second illumination window 112 may be installed.

In the present embodiment, the description has been made assuming that the emitted light is autofluorescence. However, the present invention is not necessarily limited to this, and the measurement may be performed using other emitted light such as scattered light.
In addition, each of the above-described embodiments is merely an example of actualization in carrying out the present invention, and the technical scope of the present invention should not be construed as being limited thereto. That is, the present invention can be implemented in various forms without departing from the gist or the main features thereof.

DESCRIPTION OF SYMBOLS 10 Endoscope apparatus 100 Endoscope main body 110 Insertion part 110a Base end part 110b Tip part 110c Operable part 111 1st illumination window 112 2nd illumination window 113 1st observation window 114 2nd observation window 115 Forceps channel 120 Operation part 120a Knob 120b Inlet 130 Cable 135 Optical unit 140 Illumination optical fiber 142 Excitation optical fiber 150 Imaging element 152 Spectral area 154 Imaging area 156 Circuit board 160 Spectroscopic optical system 162 Bandpass filter 164 Slit 166 Collimating lens 168 Diffraction grating 170 Condensing lens 180 Imaging Optical system 182 Shading mask 182a Opening 184 Condensing lens 200 Endoscope processor 210 Control unit 212 Memory 220 Light source unit 222 Illumination light source 224 Excitation light source 230 Spectroscopy Analyzing unit 240 image processing unit 300 input unit 400 monitors

Claims (4)

An optical unit that receives imaging light of an observation target part of a body lumen and radiation light of a measurement target part of the body lumen,
A first light receiving region for receiving imaging light of the observation target region, and a second light receiving region for receiving radiation light of the measurement target region formed on the same light receiving surface;
An imaging optical system for guiding the imaging light to the first light receiving region;
A spectroscopic optical system for guiding the emitted light to the second light receiving region;
A housing that houses the imaging optical system and the spectroscopic optical system in parallel with the observation target part;
With
An optical unit in which a light-shielding mask having an opening for limiting the area of a light beam passing therethrough is disposed on the optical path of the imaging optical system.   The imaging optical system includes an objective optical system including one objective lens or a plurality of lenses, and the light shielding mask is disposed at a focal position of the objective lens or the objective optical system. The optical unit described.   The optical unit according to claim 1, wherein the image sensor is a monochrome type image sensor. An endoscope body having the optical unit according to claim 1 or 2,
Connected to the endoscope main body, processes imaging data of the observation target part imaged in the first light receiving region, and processes spectroscopic measurement data of the measurement target part spectroscopically measured in the second light receiving region An endoscope processor;
An endoscope apparatus comprising:

Images