JP5927077B2 - Endoscope system - Google Patents

Description

  The present invention relates to an endoscope system that acquires an image of a subject by irradiating illumination light.

  In many cases, an endoscope system is configured to acquire an image of a subject by irradiating illumination light on the assumption that ambient light cannot be used.

  For example, a scanning endoscope system that acquires an image of a subject by irradiating the subject with illumination light with directivity and receiving reflected light while scanning the illumination direction of the illumination light has been proposed. Yes.

  Japanese Patent Application Laid-Open No. 2011-19706 discloses a medical probe that scans a laser beam to observe an object, a laser light source that supplies a laser beam to the medical probe, and whether the medical probe is in a predetermined state. A medical observation system is described that includes a determination unit that determines whether or not, and a control unit that controls the amount of laser light emitted from the laser light source based on a determination result by the determination unit. And by such a structure, it is supposed that it becomes possible to restrict | limit the light quantity of a laser beam to a safe level in the condition where a laser beam enters an operator's eyes.

  In the technology described in Japanese Patent Publication No. 2010-520778, the optical fiber guides light from the light source at the proximal end to the distal end, where the piezoelectric material tube is the distal end of the optical fiber. A force is applied to cause scanning to be performed in a desired pattern. Light from the distal end of the optical fiber passes through the lens system and is reflected at least partially toward the side of the side view scope by the reflecting surface to illuminate tissue within the patient's body. The light received from the internal tissue is reflected and returned to the collecting optical fiber that directs the light to the proximally located photodetector or directly back to the distal photodetector. The photodetector generates an electrical signal indicative of the intensity of light that can be used to generate an image of the internal tissue. It is said that the light received from the tissue can be either scattered light, polarized light, fluorescent light, or filtered light, depending on the illumination light.

  Japanese Patent Application Publication No. 2010-525921 discloses a method of adjusting image acquisition among a plurality of endoscopes. The method irradiates a surface image with light in the first endoscope system, collects backscattered light, and generates an image based on the collected backscattered light. Includes steps to acquire. The intensity of light from the first endoscope system is reduced. The image of the surface is backscattered light at different times while the surface is scanned with the beam with the second scanning beam endoscope system and the surface is scanned with the beam while the light intensity is decreasing. It is obtained by collecting. In one aspect, adjustment signals are exchanged between the endoscope systems to adjust image acquisition. In another aspect, image acquisition is coordinated by the scanning beam endoscope system detecting a decrease in intensity.

  Japanese Unexamined Patent Application Publication No. 2009-11809 discloses a medical instrument (40) including a treatment part (41) for performing a treatment operation on a living tissue, and a treatment part movement for moving the position of the treatment part of the medical instrument. A mechanism (60), a treatment detection unit (20a) for detecting that the treatment part is in a treatment state or a non-treatment state, and a treatment part moving mechanism by controlling the treatment part moving mechanism according to a detection result by the treatment detection part And a control unit (20) for controlling the movement of the medical system. And by such a structure, it is supposed that the medical system with sufficient operativity which can switch the moving speed of a treatment tool reliably and easily at the time of treatment of a treatment tool can be implement | achieved.

  By the way, various light sources are used as a light source unit that emits illumination light. For example, a scanning endoscope system as described above needs to irradiate illumination light with directivity to a subject. In order to obtain light with high directivity, a laser light source or the like that can obtain coherent light is used.

  Laser light emitted from such a light source has a high energy density. Therefore, when the endoscope is outside the subject so that high-intensity light does not enter the eye of the surgeon, the light source The amount of light emitted from the unit is reduced to a safe level.

  Specifically, in the above-described Japanese Patent Application Laid-Open No. 2011-19706, whether or not the endoscope is outside the subject is determined by light (external factor light) at a timing when illumination light is not emitted from the scanning endoscope. ) Is determined according to whether light is received or not. That is, when external factor light that is not return light of illumination light from the subject is received, it is determined that the light is external light, that is, the endoscope is outside the subject.

JP 2011-19706 A Special table 2010-520778 JP 2010-525921 A JP 2009-11809 A

  However, when using a treatment instrument that performs treatment with light emission on the subject, such as an electrosurgical knife or a therapeutic laser, the endoscope is located inside the subject. In some cases, it is determined that the endoscope is outside the subject, the amount of illumination light is reduced, and the observed image becomes dark.

  The present invention has been made in view of the above circumstances, improves the detection accuracy of whether or not the subject is in the subject, and the image observed during observation with the endoscope becomes dark. An object of the present invention is to provide an endoscope system that can reduce the occurrence of such a situation.

In order to achieve the above object, an endoscope system according to an aspect of the present invention includes a light source unit that emits illumination light, a light guide unit that guides the illumination light and irradiates the subject from a tip, A treatment tool for performing a treatment involving light emission on the subject, and a treatment that supplies and controls a drive current to the treatment tool to output a logic signal indicating whether or not the treatment tool is operated. A control device, a return light detection unit for detecting return light from the subject irradiated with the illumination light, an external factor light detection unit for detecting external factor light other than the return light, and the external factor light Is detected, the amount of illumination light emitted from the light source unit is maintained at a predetermined amount based on the logic signal indicating that the treatment instrument is operating, and the treatment instrument is not operating. based on the logic signal indicating that emission of the illumination light from the light source unit Are you and a dimmer to lower than the predetermined amount.

  According to the endoscope system of the present invention, it is possible to improve the detection accuracy of whether or not the subject is in the subject, and the image observed during the observation with the endoscope becomes dark. It becomes possible to reduce.

The figure which shows the structural example of the scanning endoscope system in Embodiment 1 of this invention. The figure which shows the mode of the optical scanning in the scanning endoscope system of the said Embodiment 1. FIG. In the said Embodiment 1, the figure which shows a mode that the light which generate | occur | produced with the treatment tool exists in an observation visual field. In the said Embodiment 1, a timing chart which shows a scanning drive voltage, a shutter, interruption | blocking / irradiation period, an optical detection part output, treatment tool operation | movement, and emitted light quantity. The chart for demonstrating the logical operation of light emission amount adjustment based on the presence or absence of external factor light, and the operation state of a treatment tool in the said Embodiment 1. FIG. 7 is a flowchart showing a light amount control operation of the light source unit by the light control unit of the first embodiment. The figure which shows the structural example of the scanning endoscope system in Embodiment 2 of this invention.

Embodiments of the present invention will be described below with reference to the drawings.
[Embodiment 1]

  1 to 6 show Embodiment 1 of the present invention, and FIG. 1 is a diagram showing a configuration example of a scanning endoscope system 1.

  The scanning endoscope system 1 of the present embodiment includes a light source unit 2, an optical fiber 3, a shutter 4, an intermittent emission control unit 5, an endoscope 6, a drive element 7, and a scan drive unit 8. , An optical fiber bundle 9, a light detection unit 12, an image processing unit 15, a monitor 16, a light control unit 18, a treatment tool 21, and a treatment tool control device 22.

  The light source unit 2 emits illumination light, for example, illumination light of a plurality of colors, specifically, a red light emitting laser that emits red (R) narrowband light, and green that emits green (G) narrowband light. A light emitting laser and a blue light emitting laser that emits blue (B) narrow band light are emitted to emit color illumination light. Here, the laser is used as the light source because coherent light is emitted, so that it is possible to obtain a light beam that is less diffused (that is, highly directional). Here, the light source unit 2 is assumed to emit color illumination light having RGB three-color components. However, it is of course possible to emit monochrome illumination as long as it is sufficient to acquire a monochrome image. Absent. Alternatively, it may emit light such as ultraviolet light, infrared light, or light for narrow band imaging (NBI).

  The optical fiber 3 is a light guide unit that guides the illumination light emitted from the light source unit 2 and irradiates the subject with directivity from the tip, and is, for example, a single mode type in order to suppress the diffusion of the emitted light. An optical fiber is used. The tip of the optical fiber 3 is disposed at the tip of the endoscope 6. The irradiated illumination light is reflected by the subject to become return light, and enters from the tip of the optical fiber bundle 9.

  The shutter 4 and the intermittent emission control unit 5 control the illumination period for irradiating the illumination light from the tip of the optical fiber 3 and the cutoff period for blocking the illumination light from the tip of the optical fiber 3 at a predetermined cycle. It is a control unit. That is, the shutter 4 is arranged on the light guide path by the optical fiber 3 and switches whether the illumination light emitted from the light source unit 2 is guided to the front end side of the optical fiber 3 or blocked. The intermittent emission control unit 5 drives the shutter 4 to control the irradiation period and the cutoff period.

  The endoscope 6 is for insertion into a subject. The optical fiber 3 and the optical fiber bundle 9 are inserted through the endoscope 6 and a driving element 7 is also provided.

  The driving element 7 and the scanning driving unit 8 are scanning units that perform scanning that changes the direction of the tip of the optical fiber 3. The drive element 7 is a drive source that moves the tip of the optical fiber 3, and is configured as, for example, a piezo element. The scan driver 8 is a driver that controls the drive current supplied to the drive element 7.

  The optical fiber bundle 9 has a distal end disposed at the distal end of the endoscope 6 and receives return light from the subject and guides it to the proximal end side. The optical fiber bundle 9 performs light reception with a wide directivity capable of receiving light from all directions within the scanning range of the optical fiber 3.

  The light detection unit 12 detects the return light guided through the optical fiber bundle 9, so that the light from the scanning range at the tip of the optical fiber 3 by the driving element 7 and the scanning driving unit 8 has a wide directivity. It is to detect. The light detection unit 12 functions as a return light detection unit that detects return light from the subject irradiated with illumination light during the irradiation period, and detects external factor light that detects external factor light other than return light during the blocking period. It comes to function as a part.

  Based on the information on the direction of the tip of the optical fiber 3 from the scanning drive unit 8, the image processing unit 15 calculates from which direction the return light detected by the light detection unit 12 is detected. Thus, an image is constructed and output to the monitor 16.

  The monitor 16 displays the image formed by the image processing unit 15.

  The treatment tool 21 is for performing a treatment involving light emission on the subject. Examples of such a treatment tool 21 include an electric knife and a therapeutic laser. Further, the band of light emitted from the treatment instrument 21 is not limited to the visible light range, and may be the above-described ultraviolet light or infrared light, or any other band that is detected by the light detection unit 12. I do not care.

  The treatment instrument control device 22 supplies a drive current to the treatment instrument 21 and controls it.

  The light control unit 18 is based on the detection result of the external factor light obtained by the light detection unit 12 obtained via the image processing unit 15 and the information on the driving state of the treatment tool 21 obtained from the treatment tool control device 22. It is determined whether the endoscope 6 is inside or outside the subject, and the amount of light emitted from the light source unit 2 is controlled based on the determination result.

  Next, FIG. 2 is a diagram showing a state of optical scanning in the scanning endoscope system 1.

  The scanning of the tip of the optical fiber 3 by the driving element 7 and the scanning driving unit 8 is performed as shown in FIG. 2, for example.

  That is, the direction change starts from the center point A of the observation visual field 16a, the direction of the tip of the optical fiber 3 is changed along the spiral path, and the farthest point B farthest from the center is reached. To reach. After that, after turning off the illumination light to the subject, the direction of the tip of the optical fiber 3 may be returned from the farthest point B to the center point A, or the same operation may be performed. May follow the spiral path in the reverse direction to return to the center point A, or other methods may be employed. For the sake of convenience, in the present embodiment, it is assumed that a method is employed in which the spiral path is traced in the reverse direction from the farthest point B and returned to the center point A.

  As described above, the light detection unit 12 detects light with a wide directivity capable of receiving all light from the scanning range as shown in FIG. Accordingly, it cannot be determined from only the detection result of the light detection unit 12 which point in the scanning range the light detected by the light detection unit 12 is.

  Therefore, the image processing unit 15 receives information on the direction of the tip of the optical fiber 3 from the scanning drive unit 8 (that is, information on the irradiation direction of the illumination light), and the detection result of the light detection unit 12 is the result of the optical fiber 3. The image is constructed by mapping the detection result of the light detection unit 12 to the estimated position, presuming that it is due to the return light from the subject in the direction of the tip.

  Next, FIG. 3 is a view showing a state in which the light generated by the treatment instrument 21 is present in the observation visual field 16a.

  In the example shown in FIG. 3, when an examination is performed with the endoscope 6 together with the treatment tool 21, light emitted from the treatment tool 21 (light that is not return light of illumination light) is observed in the observation visual field 16 a. : Shows the appearance of external factor light 21a). However, whether the external factor light 21a detected by the light detection unit 12 during the blocking period is due to light emitted from the treatment instrument 21 or whether it is due to external light when the endoscope 6 is outside the subject. Cannot be determined only from the detection result of the light detection unit 12. Therefore, as will be described later, the operating state of the treatment instrument 21 is detected, and the detection result is used to make a more accurate determination.

  Next, FIG. 4 is a timing chart showing the scanning drive voltage, the shutter, the cutoff / irradiation period, the output of the light detection unit 12, the operation of the treatment instrument 21, and the amount of emitted light.

  The scan drive voltage of the current supplied from the scan drive unit 8 to the drive element 7 has a waveform as shown in FIG. 4, for example. In this waveform, the starting point at which the amplitude of the scanning drive voltage fluctuates is the point at which scanning starts from the center point A shown in FIG. 2, and the point at which the amplitude of the scanning driving voltage reaches the maximum value is shown in FIG. It is a point that reaches the farthest point B shown. Thereafter, since the spiral path is traced back to the center point A from the farthest point B, the amplitude of the scanning drive voltage gradually decreases. Thus, an image for two frames is acquired until the amplitude of the scanning drive voltage reaches the maximum value from 0 and returns to 0 again. The period during which images for two frames are acquired is an irradiation period in which the shutter 4 is open, that is, the illumination light is irradiated from the tip of the optical fiber 3.

  After this irradiation period, it becomes a blocking period in which irradiation of illumination light from the tip of the optical fiber 3 is blocked, and at this time, the scanning drive voltage also has an amplitude of zero. The signal indicating the cutoff / irradiation period is created by the intermittent emission control unit 5 by inverting the signal for driving the shutter 4 to normalize the amplitude, and takes a signal value of 1 during the cutoff period. It is assumed that the signal value 0 is taken during the period. A signal indicating this blocking / irradiation period is output from the intermittent emission control unit 5 to the image processing unit 15.

  On the other hand, the detection signal of the light detection unit 12 shows different waveforms depending on whether or not the external factor light 21a is present. When there is no external factor light 21a, the output signal of the light detection unit 12 is 0 in the blocking period, and a signal value corresponding to the amount of return light from the subject portion irradiated with the illumination light only in the irradiation period. Show. On the other hand, when the external factor light 21a is present, the output signal of the light detection unit 12 indicates a signal value corresponding to the light amount of the external factor light 21a during the cutoff period, and according to the light amount of the return light during the irradiation period. A value obtained by adding a signal value corresponding to the light quantity of the external factor light 21a to the obtained signal value.

  The image processing unit 15 calculates a product of the signal indicating the blocking / irradiation period input from the intermittent emission control unit 5 and the detection signal from the light detection unit 12, thereby extracting a signal for only the blocking period. be able to. The signal extracted here indicates a signal value of zero when there is no external factor light 21a, and indicates a non-zero signal value when there is external factor light 21a. The image processing unit 15 outputs a signal having a signal value of zero as a signal having a logical value of 0 and a signal having a non-zero signal value as a signal having a logical value of 1 to the dimming unit 18. Therefore, a logical value 0 indicates that there is no external factor light 21a, and a logical value 1 indicates that there is an external factor light 21a. The image processing unit 15 outputs such a logic signal in real time during the interruption period, but continues to output the logic signal at the final point in the immediately preceding interruption period during the irradiation period.

  On the other hand, the treatment instrument control device 22 outputs a logic signal indicating whether or not the treatment instrument 21 is in operation to the dimming unit 18 in real time. Here, the logic signal output from the treatment instrument control device 22 is, for example, a signal that takes a logical value 1 when the treatment instrument 21 is operated and takes a logical value 0 when the treatment instrument 21 is not operated. .

The light control unit 18 performs the logical operation as shown in FIG. 5 based on the logical signal received from the image processing unit 15 and the logical signal received from the treatment instrument control device 22 , thereby illuminating from the light source unit 2. It is determined whether the amount of emitted light is set to a normal value (that is, maintained at a predetermined amount) or lower than the normal value (predetermined amount). FIG. 5 is a chart for explaining the logical operation of the light emission amount adjustment based on the presence / absence of the external factor light 21 a and the operation state of the treatment instrument 21.

When the logical value input to the dimmer 18 is the above-described value, the logical operation shown in FIG. 5 is performed as shown in the following Equation 1.
[Equation 1]
X = Aand (notB)
Here, the logical input from the image processing unit 15 is A, the logical input from the treatment instrument controller 22 is B, the operation result is X, the logical product is “and”, and the negative is “not”. As for the calculation result, X = 1 indicates a decrease in light amount (and consequently, a determination result that the endoscope 6 is outside the subject), and X = 0 indicates a normal light amount (and thus the endoscope 6 is in the subject). It is assumed that a determination result is present).

  The graph of the amount of emitted light in FIG. 4 changes from operating (ON) to non-operating (OFF) as shown in the graph with respect to the output of the light detection unit 12 when the external factor light 21a is present. It shows the situation when

  FIG. 6 is a flowchart showing the light amount control operation of the light source unit 2 by the light control unit 18.

  The light control unit 18 determines whether there is the external factor light 21a based on the logic signal input from the image processing unit 15 (step S1).

  Here, when it is determined that the external factor light 21a is present, it is next determined whether or not the treatment instrument 21 is operating based on the logic signal input from the treatment instrument control device 22 (step). S2).

  Here, when it is determined that the treatment instrument 21 is not in operation, the light control unit 18 controls the light source unit 2 so that the eyes of the operator or the like can be obtained even when the endoscope 6 is outside the subject. The amount of emitted light is reduced to a safe level where high intensity light is not incident (step S3).

  If it is determined in step S1 that there is no external factor light 21a, or if it is determined in step S2 that the treatment instrument 21 is operating, an operation for turning off the light source unit 2 has been performed. It is determined whether or not (step S4).

  If the power is not turned off, the process returns to step S1 and the above-described processing is repeated. On the other hand, if the power is turned off, the processing is terminated.

  According to the first embodiment, even when the external factor light 21a is detected, when the treatment instrument 21 is operating, the amount of illumination light emitted from the light source unit 2 is maintained at a predetermined amount. Therefore, it is possible to prevent the external factor light 21a emitted from the treatment instrument 21 from being misidentified as external light.

In this way, it is possible to improve the detection accuracy as to whether or not the subject is in the subject, and to reduce the darkness of the image observed during the observation with the endoscope 6.
[Embodiment 2]

  FIG. 7 shows Embodiment 2 of the present invention and is a diagram showing a configuration example of the scanning endoscope system 1. In the second embodiment, the same parts as those in the first embodiment are denoted by the same reference numerals and the description thereof is omitted as appropriate, and only different points will be mainly described.

  In the first embodiment described above, since the presence or absence of the external factor light 21a is detected based on the output signal of the light detection unit 12 in the blocking period, it cannot be detected in real time in the irradiation period. In contrast, in the present embodiment, a detection unit for detecting external factor light is separately provided so that the presence / absence of the external factor light 21a can be detected in real time in both the blocking period and the irradiation period. It has become a thing.

  That is, the scanning endoscope system 1 according to the present embodiment is configured to transmit light emitted from the proximal end of the optical fiber bundle 9 to the scanning endoscope system 1 illustrated in FIG. A beam splitter 11 is provided on the optical path.

The beam splitter 11 is a light beam of illumination light emitted from the light source unit 2 (for example, the laser light bands of the red, green, and blue lasers described in paragraph [0020] of this specification ). Is reflected, and light in other bands is transmitted.

  On the optical path of the reflected light of the beam splitter 11, a return light detection unit 12 a for detecting return light of illumination light from the subject is disposed, and the detection result is output to the image processing unit 15. It has become.

Further, on the optical path of the transmitted light of the beam splitter 11, the external factor light 21a (more precisely, light in a band different from the light detected by the return light detection unit 12a included in the external factor light 21a) is detected. An external factor light detection unit 12b is provided for this purpose. The band detected by the external factor light detection unit 12b may be a visible light region other than the above-described illumination light ( laser light ) region, or an infrared light region or an ultraviolet light region other than the visible light region. It doesn't matter. The external factor light detector 12b is configured to output the above-described logic signal indicating whether or not the external factor light 21a is present to the dimmer 18 based on the detection result.

  According to the second embodiment, the external factor light detection unit 12b detects the light in the band different from the light detected by the return light detection unit 12a while having the same effect as the first embodiment. Therefore, the presence / absence of the external factor light 21a can be detected in real time in both the blocking period and the irradiation period, and the amount of illumination light emitted from the light source unit 2 can be controlled not only in the blocking period but also in the irradiation period. Can also be performed in real time.

  As a result, for example, a difference occurs in the following case.

  Even if the external factor light 21a is generated during the irradiation period when the external factor light 21a was not detected in the immediately preceding cutoff period when the treatment instrument 21 is not operating, the configuration of the first embodiment has the next cutoff period. The generation of the external factor light 21a could not be detected until it came, that is, it had to wait until the next cutoff period to reduce the illumination light quantity. On the other hand, in the configuration of the present embodiment, since it can be detected when the external factor light 21a is generated, the amount of illumination light can be reduced in real time.

  Further, it is assumed that the external factor light 21a is detected in a certain interruption period, and the treatment instrument 21 changes from operating to non-operating in the subsequent irradiation period. In this case, in the configuration of the first embodiment, regardless of whether or not the endoscope 6 actually goes out of the subject, the remaining period after the change during the non-operation in the irradiation period is equal to the illumination light. The amount of light will decrease. In the subsequent blocking period, if the external factor light 21a is detected, the decrease in the amount of illumination light is maintained, but if the external factor light 21a is not detected, the illumination light amount is returned to normal again. That is, in the configuration of the first embodiment, there is a case where the amount of illumination light temporarily decreases for a short time. In contrast, in the configuration of the present embodiment, the amount of illumination light is reduced if the external factor light 21a is detected after the time when the treatment instrument 21 changes to non-operation, but the external factor light 21a is detected. Otherwise, the illumination light quantity is maintained as usual, so that it is possible to continue observing the endoscopic image with appropriate brightness, and avoid a temporary decrease in the light quantity.

  Although the endoscope system has been mainly described above, a control device or a control method for controlling the light amount of the light source unit of the endoscope system as described above may be used, or a light source of the endoscope system may be added to a computer. It may be a control program for controlling the unit as described above, a computer-readable recording medium for recording the control program, or the like.

  Further, the present invention is not limited to the above-described embodiments as they are, and can be embodied by modifying the constituent elements without departing from the scope in the implementation stage. Moreover, various inventions can be formed by appropriately combining a plurality of constituent elements disclosed in the embodiment. For example, you may delete some components from all the components shown by embodiment. Furthermore, the constituent elements over different embodiments may be appropriately combined. Thus, it goes without saying that various modifications and applications are possible without departing from the spirit of the invention.

DESCRIPTION OF SYMBOLS 1 ... Scanning endoscope system 2 ... Light source part 3 ... Optical fiber (light guide part)
4. Shutter (lighting control unit)
5. Intermittent emission control unit (lighting control unit)
6 ... Endoscope 7 ... Drive element (scanning part)
8. Scanning drive unit (scanning unit)
DESCRIPTION OF SYMBOLS 9 ... Optical fiber bundle 11 ... Beam splitter 12 ... Photodetection part (return light detection part, external factor light detection part)
DESCRIPTION OF SYMBOLS 12a ... Return light detection part 12b ... External factor light detection part 15 ... Image processing part 16 ... Monitor 16a ... Observation visual field 18 ... Dimming part 21 ... Treatment tool 21a ... External factor light 22 ... Treatment tool control apparatus

Claims (5)

A light source that emits illumination light;
A light guide that guides the illumination light and irradiates the subject from the tip; and
A treatment tool for performing a treatment involving light emission on the subject;
A treatment instrument control device for supplying a drive current to the treatment instrument to control and outputting a logic signal indicating whether or not the treatment instrument is operating;
A return light detection unit for detecting return light from the subject irradiated with the illumination light;
An external factor light detector for detecting external factor light other than the return light; and
When the external factor light is detected , based on the logic signal indicating that the treatment instrument is operating, the light emission amount of the illumination light from the light source unit is maintained at a predetermined amount, and the treatment instrument is A dimming unit that reduces a light emission amount of illumination light from the light source unit below the predetermined amount based on the logic signal indicating that it is not operating;
An endoscope system comprising: An illumination control unit that controls an irradiation period of irradiating the illumination light from the tip of the light guide unit and a blocking period of blocking irradiation of the illumination light from the tip of the light guide unit at a predetermined period;
A light detection unit for detecting light;
Further comprising
The endoscope system according to claim 1, wherein the light detection unit functions as the return light detection unit in the irradiation period and functions as the external factor light detection unit in the blocking period.   The endoscope system according to claim 1, wherein the external factor light detection unit detects light in a band different from light detected by the return light detection unit. A scanning unit that performs scanning to change the direction of the tip of the light guide unit;
Based on the information on the direction of the tip of the light guide from the scanning unit, an image processing unit that forms an image from the detection result of the return light detection unit;
The endoscope system according to claim 1, further comprising:   The endoscope system according to claim 1, wherein the treatment instrument is an electric knife or a therapeutic laser.

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