JP2017086549A - Scanning endoscope apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a scanning endoscope apparatus with which the operator can easily understand from an image displayed on a display unit that the tip of the scanning endoscope is outside the subject body when the tip is not within the subject.SOLUTION: Current detection circuits 37a, 37b detect the currents of drive signals flowing through the piezoelectric elements constituting an actuator 16 mounted within the tip of a scanning endoscope 2. A determination circuit 25c calculates the resistance values of the piezoelectric elements using the information of the then-current drive voltages. The determination circuit next obtains the temperatures of the piezoelectric elements from table data in which resistance values and temperatures stored in memory 24 are associated with each other, determines whether the tip of the endoscope is within or outside the patient body, based on whether the temperatures are within the temperature range showing the tip is placed within the patient, and when the tip is outside the patient body, displays on a monitor 4 a second image of which resolution is lower than that of a first image.SELECTED DRAWING: Figure 5

Description

  The present invention relates to a scanning endoscope apparatus that scans illumination light on a subject.

In recent years, endoscopes have been widely used in the medical field and the like. Various techniques have been proposed to reduce the diameter of the insertion portion inserted into the subject. An example of such a technique is a scanning endoscope apparatus.
For example, as a conventional example, Japanese Patent Application Laid-Open No. 2011-19706 discloses that in a situation where laser light enters the eyes of an operator or the like, the amount of laser light can be limited to a safe level. Based on a probe that scans a laser beam, a laser light source that supplies the probe with the laser beam, a determination unit that determines whether or not the probe is in a predetermined state such as inside the body, and a determination result by the determination unit Thus, a scanning endoscope apparatus is disclosed that includes control means for controlling the light quantity of the laser light source emitted from the laser light source.

JP 2011-19706 A

The above conventional example discloses that, in the case of a determination result that the probe or the like is not in a predetermined state such as the inside of the body, the output of the laser beam is limited and the monitor displays that the light amount of the laser beam is limited. There is a possibility of erroneous determination. In particular, if the output of the laser beam does not decrease due to a misjudgment despite the fact that the tip of the probe or the scanning endoscope is actually outside the body, the laser beam is not decreased. It is desirable to be able to recognize or confirm the user so that the user can be protected quickly.
The present invention has been made in view of the above points. When the distal end portion of the scanning endoscope is outside the body, the distal end portion of the scanning endoscope is easily covered from the image displayed on the display device. An object of the present invention is to provide a scanning endoscope apparatus that can recognize that it is outside a specimen.

  The scanning endoscope apparatus according to one aspect of the present invention includes a fiber having a first end where incident light is incident and a second end that emits the illumination light toward the subject, and the second end. A scanning endoscope comprising: a scanning section that vibrates so as to form a spiral trajectory; a detection element that detects reflected light from the subject side and outputs a detection signal; and the second end section A determination unit that determines whether the distal end portion of the scanning endoscope in which the scanning endoscope is located is inside or outside the subject, and the distal end portion is inside the subject as a determination result by the determination unit The first image signal of the first image generated from the detection signal is output to a display device, and when the tip is outside the subject, the first image is output from the detection signal. Image information relating to the subject compared to the first image signal, which is different from the display form of It is converted into the second image signal of the small second image having a signal processing unit for outputting to the display device.

  According to the present invention, when the distal end portion of the scanning endoscope is outside the body, it is easily recognized from the image displayed on the display device that the distal end portion of the scanning endoscope is outside the subject. it can.

FIG. 1 is a diagram showing an overall configuration of a scanning endoscope apparatus according to a first embodiment of the present invention. FIG. 2 is a cross-sectional view showing the configuration of the actuator taken along line AA in FIG. FIG. 3 is a diagram showing a waveform of a drive signal for driving the actuator. FIG. 4 is a diagram showing a trajectory where the tip of the optical fiber is swung by the drive signal of FIG. FIG. 5 is a diagram showing the configuration of the periphery of the drive unit in the first embodiment. FIG. 6 is a flowchart showing typical processing contents in the first embodiment. FIG. 7 is a diagram illustrating an image display example when reduced display is selected as the second image. FIG. 8 is a diagram illustrating an image display example when monochrome display is selected as the second image. FIG. 9 is a diagram illustrating an image display example when the resolution degradation display is selected as the second image. FIG. 10 is a diagram showing an image display example when information superposition display is selected as the second image. FIG. 11 is a diagram showing the configuration of the periphery of the drive unit in a modification of the first embodiment.

Hereinafter, embodiments of the present invention will be described with reference to the drawings.
(First embodiment)
As shown in FIG. 1, a scanning endoscope apparatus 1 according to the first embodiment of the present invention includes a scanning endoscope 2 inserted into a body cavity or a body of a patient 5 forming a subject, and a scanning type. A main body device (or a scanning endoscope control device) 3 to which the endoscope 2 is detachably connected and a monitor 4 as a display device connected to the main body device 3 are provided. The scanning endoscope 2 has a memory 6 in which scope ID data including information unique to each scanning endoscope 2 is stored. This memory 6 is a scope connector (simply, (Abbreviated as “connector”) 7 is provided on a connector board 8 in the board. In addition, an input device 9 for inputting a signal for a user such as an operator to select or instruct the image display mode to the main body device 3 is provided.
The scanning endoscope 2 has an insertion portion 11 formed with an elongated shape and flexibility that can be inserted into the body or body cavity of a patient 5, and a scanning type is provided at the proximal end of the insertion portion 11. A connector 7 is provided for detachably connecting the endoscope 2 to the main body device 3. The connector 7 is detachably connected to a connector receptacle (receptacle) 7a (see FIG. 5) of the main unit 3.

An illumination optical fiber 13 serving as a light guide member for guiding illumination light supplied from the light source unit 21 of the main body device 3 is inserted into the insertion portion 11 from the base end portion to the vicinity of the distal end portion 11a. The illumination optical fiber 13 guides the illumination light incident on the first end serving as the base end, and from the distal end serving as the second end of the illumination optical fiber 13 through the concentrating optical system 14 facing, Illumination light is emitted toward an examination site (also referred to as a subject) in the patient 5.
Further, a light receiving optical fiber 15 that receives the return light from the subject and guides it to the detection unit 23 that constitutes the detection unit of the main body device 3 is inserted into the insertion unit 11.
The first end portion which becomes the light incident surface in the illumination optical fiber 13 is connected to the end portion 13c (see FIG. 5) on the distal end side of the illumination optical fiber 13b provided in the main body device 3 in the optical connector 13a. The end of the illumination optical fiber 13b that serves as the light incident surface on the proximal end side is disposed in the vicinity of the multiplexer 32 in the light source unit 21.
In addition, the second end portion serving as the light exit surface of the illumination optical fiber 13 is disposed at a position facing the condensing optical system 14 provided at the distal end portion 11a of the insertion portion 11 in the vicinity thereof. It is swung by an actuator 16 constituting a scanning unit.

An end portion that becomes a light incident surface of the light receiving optical fiber 15 is arranged along a circle, for example, around the light emitting surface of the condensing optical system 14 at the distal end surface of the distal end portion 11 a of the insertion portion 11. Further, the base end side end portion 15a serving as a light emitting surface of the light receiving optical fiber 15 is connected to a tip end side end portion 15c (see FIG. 5) of the light receiving optical fiber 15b provided inside the main body device 3. The proximal end side of the light receiving optical fiber 15b is disposed in the vicinity of the detector 37 in the detection unit 23.
Further, the detection unit 23 is not limited to the one provided in the main body device 3, and may be provided in the scanning endoscope 2.
The condensing optical system 14 forms an optical system having an achromatic function composed of a convex lens 14a and a concave lens 14b, condenses illumination light from the distal end surface of the illumination optical fiber 13, and emits it to the subject side.
Inside the distal end portion 11 a of the insertion portion 11, the distal end side of the illumination optical fiber 13 is orthogonal to the longitudinal direction of the illumination optical fiber 13 based on a drive signal output from the drive unit 22 of the main body device 3. An actuator 16 constituting a scanning unit for driving in the direction is provided.

Piezoelectric elements 17a, 17b and 17c, 17d (see FIG. 2) constituting the actuator 16 are connected to drive lines 18a, 18b inserted into the insertion portion 11, and the drive lines 18a, 18b serve as electrical contacts of the connector 7. To the drive lines 18c and 18d in the main unit 3. The drive lines 18c and 18d are connected to the drive unit 22 and applied with a drive signal.
When the longitudinal direction of the illumination optical fiber 13 is set to the Z-axis direction, the actuator 16 extends or contracts in the Z-axis direction by applying a drive signal, thereby illuminating as shown by the dotted line from the state shown by the solid line in FIG. The distal end side of the optical fiber 13 is moved, and the illumination light emitted from the distal end surface of the illumination optical fiber 13 is scanned in the X and Y axis directions perpendicular to the Z axis.
When the actuator 16 is driven by applying a drive signal, the base end portion of the actuator 16 along the Z-axis direction is supported by a support member so that the distal end side of the illumination optical fiber 13 can be easily scanned in the X- and Y-axis directions. It is fixed to the inner surface of the insertion portion 11 via 19.
The illumination optical fiber 13 and the actuator 16 are arranged so as to have a positional relationship as shown in FIG. 2, for example, in a cross section perpendicular to the longitudinal axis direction of the insertion portion 11. FIG. 2 is a cross-sectional view showing a configuration of the actuator 16 provided in the scanning endoscope 2.

As shown in FIG. 2, a ferrule 41 as a joining member is disposed between the illumination optical fiber 13 and the actuator 16. Specifically, the ferrule 41 is made of, for example, zirconia (ceramic) or nickel.
As shown in FIG. 2, the ferrule 41 is formed to have a square quadrangular prism shape, and the illumination optical fiber 13 that passes through the hole along the central axis is fixed, and the Y-axis direction (on the paper surface) Piezoelectric elements 17a, 17b and 17c, 17d forming the actuator 16 are attached to both side surfaces in the vertical direction and both side surfaces in the X-axis direction (left and right direction on the paper).
Each piezoelectric element is made of, for example, PZT (lead zirconate titanate) or the like, and expands and contracts in the longitudinal direction (Z-axis direction in FIG. 2) when a drive signal is applied. Therefore, in the state where the base end is held or fixed, for example, by applying a drive signal having an opposite phase (expanding one and contracting the other) to the piezoelectric elements 17a and 17b, light reception is performed as shown by a dotted line in FIG. The distal end side of the optical fiber 15 for use can be vibrated (oscillated) in the vertical direction.
Each of the piezoelectric elements 17a to 17d is provided with electrodes (not shown) that are polarized so that the polarization direction is a predetermined direction, and a drive signal is applied to both opposing surfaces.

FIG. 3 shows the waveforms of drive signals for driving the piezoelectric elements 17a (and 17b) and (the same applies to 17c (and 17d)).
As shown in FIG. 3, the drive signals for driving the piezoelectric elements 17a (and 17b) and the piezoelectric elements 17c (and 17d) have almost the same waveform with the phase of one of the drive signals shifted, and are changed to a sine wave shape. The voltage is gradually increased from a value of 0 corresponding to the scanning start position Pa (see FIG. 4) to a value corresponding to the scanning end position Pb (see FIG. 4), and then gradually decreased again to correspond to the scanning start position Pa. The value is reset to 0.
By applying such a drive signal to the piezoelectric elements 17a (and 17b) and the piezoelectric elements 17c (and 17d), the distal end side of the illumination optical fiber 13 driven by the actuator 16 is as shown in FIG. It is moved (scanned) in a spiral shape from the scanning start position Pa to the scanning end position Pb. The illumination light emitted from the distal end of the illumination optical fiber 13 corresponding to the scanning of the distal end of the illumination optical fiber 13 is also optically scanned on the inner surface of the patient 5 in a spiral shape. The illumination light is controlled to emit pulses instead of continuous emission.

When the actuator 16 is driven with a drive signal having a drive waveform as shown in FIG. 3, the actuator 16 is actually shown in FIG. 4 due to individual differences such as the electrical characteristics of the piezoelectric elements 17 a to 17 d forming the actuator 16. The scanning position changes. Therefore, a two-dimensional coordinate position where light is actually irradiated when the actuator 16 of each scanning endoscope 2 is driven with a drive signal as shown in FIG. Calibration data obtained by calibrating the scanning position so as to obtain the appropriate coordinate position (also referred to as scanning position or irradiation position) is stored in advance in the memory 6 in the scanning endoscope 2 on which the actuator 16 is mounted. ing.
The calibration data is read out under the control of the controller 25 in a state where the scanning endoscope 2 is connected to the main body device 3 and stored in the memory 24 in the main body device 3.
As shown in FIG. 1, the main body device 3 generates illumination light and forms a light source 21 that forms a light source that supplies the illumination light generated on the proximal end side of the illumination optical fiber 13 of the scanning endoscope 2; Using a drive unit 22 that drives the tip of the illumination optical fiber 13 to scan two-dimensionally, and a light-receiving optical fiber 15 that receives the return light of the illumination light emitted from the tip of the illumination optical fiber 13. A detection unit 23 having a detector 37 as a detection element that detects return light and outputs a photoelectrically converted detection signal, and a read in which scope ID data read from the memory 6 is (temporarily) stored A memory 24 having a memory area for forming the data storage unit 24a and a controller 25 for controlling the entire main body device 3 are included.

The controller 25 and the signal generator 33 in FIG. 1 are formed by an FPGA (Field Programmable Gate Array) 30 shown by a two-dot chain line in FIG.
The light source unit 21 includes an R laser light source 31a that generates laser light in a red wavelength band (also referred to as R laser light or simply R light), and light in a green wavelength band (also referred to as laser G light or G light). A G laser light source 31b that generates blue light, a B laser light source 31c that generates laser light in a blue wavelength band (also referred to as B laser light or B light), and a multiplexer 32.
The R laser light source 31a, the G laser light source 31b, and the B laser light source 31b are configured by using, for example, a laser module 31d (see FIG. 5) using a laser diode (LD). In FIG. 5, the R laser light source 31a, the G laser light source 31b, and the B laser light source 31c are shown by one laser module 31d.
When the R laser light source 31a, the G laser light source 31b, and the B laser light source 31c in FIG. 1 are turned on under the control of the controller 25, the R laser light, the G laser light, and the B laser light are combined. 32 sequentially. The controller 25 includes a light source control circuit (or laser light control circuit) 25a that controls discrete light emission of the R laser light source 31a, the G laser light source 31b, and the B laser light source 31b. The R laser light source 31a, the G laser light source 31b, and the B laser light source 31c are also simply referred to as laser light sources 31a to 31c.

When the illumination optical fiber 13 is driven by the actuator 16, the light source control circuit 25 a emits the R laser light source 31 a and the G laser so as to emit pulses at the drive timing to the discrete coordinate positions stored in the memory 24. The light emission of the light source 31b and the B laser light source 31b is controlled.
Further, in the present embodiment, a determination circuit 25c that constitutes a determination unit that determines whether or not the distal end portion 11a of the insertion portion 11 of the scanning endoscope 2 is inserted into a patient 5 as a subject is provided. Then, based on the determination result by the determination unit, the light source control circuit 25a controls the R laser light source 31a, the G laser light source 31b, and the B laser light source 31b, and the light amount or light of the R laser light, the G laser light, and the B laser light. Control strength. Since the R, G, and B laser beams form illumination light, the light source control circuit 25a can also be defined as an illumination light control circuit that controls the amount or intensity of illumination light.
In the present embodiment, the controller 25 (the light source control circuit 25a) sends a control signal for sequentially emitting light to the R laser light source 31a, the G laser light source 31b, and the B laser light source 31b, and the R laser light source 31a, The G laser light source 31 b and the B laser light source 31 b sequentially generate R laser light, G laser light, and B laser light, and emit them to the multiplexer 32.

The multiplexer 32 sequentially supplies the R laser light from the R laser light source 31a, the G laser light from the G laser light source 31b, and the B laser light from the B laser light source 31c to the light incident surface of the illumination optical fiber 13b. The illumination optical fiber 13b sequentially supplies R laser light, G laser light, and B laser light to the illumination optical fiber 13 side.
The drive unit 22 has a function as a drive signal output unit, and includes a signal generator 33, insulating elements 36a and 36b, D / A converters 34a and 34b, and amplifiers 35a and 35b.
The drive signal generated by the drive unit 22 drives the actuator 16 mounted on the scanning endoscope 2 inserted into the patient 5, so that the secondary circuit side and the insulating element as shown by a two-dot chain line in FIG. D / A converters 34a and 34b and amplifiers 35a and 35b are arranged on the side of the patient circuit 42 electrically insulated by 36a and 36b. 1 and 5 show an electric circuit system belonging to the patient circuit 42. FIG. Note that the signal generator 33 and the like other than the patient circuit 42 in FIG. 1 belong to the secondary circuit 43 (numbers are omitted in FIG. 1).

In the present embodiment, the currents of the drive signals applied to the piezoelectric elements 17a, 17b and 17c, 17d (of the actuator 16) are detected from the amplifiers 35a, 35b via the drive lines 18c, 18a, 18d, 18b. Current detection circuits 37a and 37b are provided.
As will be described later, the current detected by the current detection circuits 37 a and 37 b is input to a determination circuit 25 c provided in the controller 25. The determination circuit 25c calculates the resistance value Z of the piezoelectric elements 17a to 17d by V / I from the drive voltage V at the time of the detected current I.
The determination circuit 25c determines whether the resistance value Z is a resistance value detected within a temperature range (for example, 35 to 37 ° C.) in a state where the distal end portion 11a is inside the patient 5, or the resistance value Z When the temperature of the piezoelectric element corresponding to is within the temperature range when the distal end portion 11a is inside the patient 5, it is determined that the distal end portion 11a is inside the patient 5, and this temperature range When the temperature deviates from the above, it is determined that the patient 5 is outside the patient's body.
In order to be able to determine whether the distal end portion 11a is inside or outside the patient 5 based on the resistance value Z, the memory 6 stores table data that previously associates the resistance values of the piezoelectric elements 17a to 17d with the temperatures. Stored. This table data is stored in the memory 24 together with the calibration data.

The determination circuit 25c reads the temperature (information) of the piezoelectric elements 17a to 17d from the table data using the calculated resistance value Z, and when the temperature is within the temperature range when the temperature is within the patient 5 Determines that the distal end portion 11a is inside the patient 5, and determines that the tip 11a is outside the body of the patient 5 when the temperature is outside this temperature range.
Based on the control of the controller 25, the signal generator 33 generates an AC signal for oscillating (or swinging) the end of the illumination optical fiber 13 on the light emitting side, and D through the insulating elements 36a and 36b. / A converter 34a and 34b to output.
Insulating elements 36a, 36b (further, 36c, 36d, 36e, which will be described later) are composed of, for example, a light emitting diode (abbreviated as LED) and a phototransistor, and convert an electrical signal into an optical signal (in the optical coupling section), Further, by adopting a configuration that converts an optical signal into an electrical signal, the secondary circuit 43 side and the patient circuit 42 side are electrically insulated in the optical coupling unit. The calibration data and the like in the memory 6 are read out by the reading circuit 39 in the patient circuit 42, input to the controller 25 through the insulating element 36e, and the controller stores it in the memory 24.

The D / A converters 34a and 34b convert the digital drive signal output from the signal generator 33 into an analog drive signal and output the analog drive signal to the amplifiers 35a and 35b, respectively.
The amplifiers 35a and 35b amplify the small-amplitude drive signals output from the D / A converters 34a and 34b, respectively, into the drive signals shown in FIG. 3, and drive lines in which the current detection circuits 37a and 37b are inserted. Output to the actuator 16 (piezoelectric elements 17a, 17b and 17c, 17d) through 18c, 18a and 18d, 18b.
The current detection circuits 37a and 37b output the detected current to the determination circuit 25c provided in the controller 25 on the secondary circuit 43 side via the insulating elements 36c and 36d.
The D / A converters 34a and 34b belonging to the patient circuit 42, the amplifiers 35a and 35b, and the like are operated from a power supply circuit (not shown) belonging to the patient circuit 42 insulated from the power supply circuit on the secondary circuit 43 side. Power is supplied.
The detection unit 23 in the main body device 3 includes a detector 37 and an A / D converter 38.

The detector 37 is configured by a photodetector such as a photodiode, and receives the return light emitted from the light emitting surface of the light receiving optical fiber 15 and converts it into an electrical signal. The light receiving optical fiber 15 guides the return light reflected from the subject side that is sequentially illuminated by the R laser light, the G laser light, and the B laser light, and the guided return light sequentially enters the detector 37. Is done. The detector 37 sequentially generates analog R, G, B detection signals corresponding to the intensity of the return light of the incident R laser light, G laser light, and B laser light, and outputs them to the A / D converter 38. To do.
The A / D converter 38 sequentially converts the analog R, G, and B detection signals sequentially output from the detector 37 into digital R, G, and B detection signals, respectively, and converts the analog R, G, and B detection signals into an image generation circuit 25b in the controller 25. Output to. In the configuration shown in FIG. 1, the R laser light source 31a, the G laser light source 31b, and the B laser light source 31c may be configured to emit pulses simultaneously. In this case, the detection unit 23 may be configured to simultaneously detect R light, G light, and B light.

The memory 24 stores in advance a control program for controlling the main device 3. In addition, information of scope ID data read from the memory 6 by the controller 25 of the main device 3 is stored in a partial memory area of the memory 24. For example, a part of the memory area in the memory 24 forms a read data storage unit 24 a that temporarily stores scope ID data read from the memory 6. The scope ID data stored in the read data storage unit 24a includes the above-described calibration data and table data.
The controller 25 controls the light source unit 21 and the drive unit 22 based on, for example, a control program stored in the memory 24.
The actuator 16 having a function as a scanning unit or an optical scanning unit has a swirling position of the illumination light irradiated to the subject based on the drive signal output from the drive unit 22 under the control of the controller 25 as described above. The illumination optical fiber 13 is swung so as to draw a locus corresponding to a predetermined scanning pattern having a shape.

The light source control circuit 25a of the controller 25 sequentially turns on the R laser light source 31a, the G laser light source 31b, and the B laser light source 31c in accordance with the information on the light emission position (or light emission timing) associated with the drive signal stored in the memory 24. Control to emit light discretely. The detection unit 23 samples and acquires the return light from the subject as R, G, B detection signals at the timing of sequential light emission, and the acquired R, G, B detection signals are stored in the memory in the image generation circuit 25b. 44 (see FIG. 5).
The controller 25 is connected to a reading circuit 39 provided on the patient circuit 42 side via an insulating element 36e, and the reading circuit 39 is connected to the memory 6 via a signal line 40. The controller 25 controls the reading circuit 39 so as to read the scope ID data from the memory 6 at the time of activation, and the read scope ID data is written into the memory 24 that can be accessed from the image generation circuit 25b or the like via the controller 25.
The image generation circuit 25b may control the reading circuit 39 to acquire the scope ID data read from the memory 6.

As shown in FIG. 5, the image generation circuit 25 b includes a first image generation circuit 51 that generates a first image signal as an image signal of a first image that is an (endoscope) image for normal observation, and a first image A second image generation circuit 52 that generates a second image signal as an image signal of a second image that is an (endoscope) image having a lower luminance level or the like. The second image generation circuit 52 has a function of an image signal conversion circuit (or image signal change circuit) 52a that performs a conversion process or a change process for generating a second image signal from the first image signal.
In the present embodiment, the image generation circuit 25b performs a determination processing circuit that performs image processing for determining whether the distal end portion 11a is inside or outside the subject from the feature amount in the first image or the second image. 53. In the case where the scanning endoscope 2 is inserted into the nasal cavity of the patient 5 as the subject, the determination processing circuit 53 includes the color of the nasal cavity (red) and the color of the nasal discharge (yellow) in the image signal. When the signal of the color of the nasal hair (black) is detected as the characteristic part, it is determined that the tip 11a is in the nasal cavity (inside the body). If such a signal is not detected, the signal is detected in the nasal cavity (inside the body). It is determined that there is no signal, and a determination signal is sent to the determination circuit 25c. The user selects whether or not to use the determination processing circuit 53 of the image generation circuit 25b (for determining whether or not the distal end portion 11a is inside or outside the patient 5) based on a selection signal from the input device 9. Can do.

Further, when the distal end portion 11a of the scanning endoscope 2 is inserted as a subject into the trachea or bronchus of the patient 5, the determination processing circuit 53 uses the color of the trachea or bronchus (red) as an image signal. When a dark part (black) signal at the branching point of the tracheal branch is detected as a characteristic part, it is determined that the tip 11a is in the trachea or bronchus (in the body), and such a signal is not detected. It is determined that it is not in the trachea or bronchus (in the body), and a determination signal is sent to the determination circuit 25c.
Note that the second image is an image different from the first image, at least the luminance level (or signal level) of which is lower than the first image, and the second image is compared with the first image. Therefore, the determination processing circuit 53 may determine whether or not the distal end portion 11a is inside the patient 5 from the first image (signal). It may be determined.
As described above, the determination circuit 25c calculates the resistance value Z of the piezoelectric elements 17a to 17d from the current detection from the current detection circuits 37a and 37b and the drive voltage at that time, and refers to the table data so that the tip 11a is It is determined whether the patient is inside the patient 5 (that is, inside the body) or outside the patient 5 (that is, outside the body). When the determination result by the determination processing circuit 53 is also used, the determination circuit 25c determines whether the distal end portion 11a is inside or outside the patient 5 as the subject based on both determination results. I do.

The determination circuit 25c sends a determination result signal indicating whether the distal end portion 11a is inside or outside the patient 5 to the light source control circuit 25a and the image generation circuit 25b, and the light source control circuit 25a and the image generation circuit 25b An operation and a control operation corresponding to the determination result signal are performed.
In the case of a determination result signal inside the patient 5, the light source control circuit 25 a displays an endoscopic image with a high image quality and appropriate brightness for easy examination or diagnosis on the monitor 4 as a display device. Control is performed so that laser light as illumination light having a predetermined light amount or light intensity is emitted to the illumination optical fiber 13 side so as to be able to.
In addition, the image generation circuit 25b (the first image generation circuit 51) receives the return light from the subject side when the laser light as the illumination light having the predetermined light amount or light intensity is irradiated on the subject side. The first image signal generated based on the obtained detection signal is output to the monitor 4, and the monitor 4 displays a first image that is an endoscopic image of moderate brightness with high image quality that is easy to perform inspection or diagnosis. To do.
On the other hand, in the case of a determination result signal outside the patient 5, the light source control circuit 25 a supposes that laser light as illumination light emitted from the distal end of the illumination optical fiber 13 is temporarily transmitted to an operator or the like. Laser light (for example, laser light having a light intensity or light intensity that is less than a fraction of the predetermined laser light) reduced to such an extent that there is no problem even when irradiated to the eyes of the user is used for illumination. Control is performed so that light is emitted to the optical fiber 13 side.

In the case of a determination result signal outside the patient 5, the image generation circuit 25 b (the second image generation circuit 52) takes a display form selected by the user from the first image signal, such as a reduced resolution display. A second image signal corresponding to (or a second image having a display form or a signal standard different from that of the first image) is generated by image processing or the like corresponding to the selected display form.
In the present embodiment, when the user observes the first image or the second image as the endoscopic image displayed on the monitor 4, it is easily recognized or visually recognized whether the image is the first image or the second image. As can be done, the image generation circuit 25b converts or changes the first image signal into a second image signal having a different resolution or the like (display mode item) from the first image signal.
Further, as described above, in the present embodiment, in the case of the determination result outside the patient 5, the laser light output is set to a value that is sufficiently lower than the internal determination result (also simply referred to as weak). At the same time, control is performed so that the second image having a resolution lower than that of the first image is displayed on the monitor 4 as a display device, and in the case of a determination result inside the patient 5, output of laser light is performed. Is set so that the output of the laser beam is sufficiently larger than the external determination result (also simply referred to as “strong”), and control is performed so that the first image having higher resolution than the second image is displayed on the monitor 4. .

That is, the strength and weakness of the laser light output correspond to (link) the first image and the second image displayed on the monitor 4. Therefore, for example, when the operator performs an operation of pulling out the insertion portion 11 from the inside of the patient 5 (including the distal end portion 11a), an image displayed on the monitor 4 (in this case, the first image) ) And whether or not the output has changed from strong to weak laser light can be easily and quickly recognized based on whether or not the image has changed to a reduced resolution image (in this case, the second image). (When the operation of pulling out the tip portion 11a to the outside is performed, the laser beam actually emitted from the tip portion 11a is strong or weak. This is much simpler than the case of recognition and judgment from state observation etc.).
For this reason, if an erroneous determination occurs, the operator can easily recognize that the output of the laser beam remains strong because the image resolution or the like does not change in the above operation, and the output is strong. It becomes easy to perform an operation for protecting other surgeons or surrounding medical staff from the laser beam.
Further, as described above, the intensity and weakness of the output of the laser beam are linked with the difference in the resolution of the displayed image. Therefore, in the case of the determination result outside the patient 5, the illumination optical fiber Since the light amount or light intensity of the laser light emitted from the tip of 13 is weakly reduced, the brightness level or brightness of the second image is an image that is sufficiently reduced as compared to the first image. For this reason, it is also possible to use a display form or image processing that generates a second image signal in which information in the external case is simply superimposed on the first image signal.
In the configuration example shown in FIGS. 1 and 5, the image generation circuit 25b forming the signal processing unit does not include the determination circuit 25c. For example, as shown by a dotted line in FIG. The circuit 25b may include the determination circuit 25c. Alternatively, a signal processing unit including the image processing circuit 25b and the determination circuit 25c indicated by a solid line may be defined.

The scanning endoscope apparatus 1 according to the present embodiment forms a fiber having a first end where incident light is incident and a second end that emits the illumination light toward the patient 5 forming the subject. A scanning endoscope 2 including an illumination optical fiber 13, an actuator 16 that forms a scanning unit that vibrates the second end so as to form a spiral locus, and reflection from the subject side. A detector 37 that forms a detection element that detects light and outputs a detection signal, and a distal end portion 11a of the scanning endoscope 2 on which the second end portion is disposed are inside or outside the subject. A determination circuit 25c that forms a determination unit that determines whether or not there is a first image of the first image that is generated from the detection signal when the tip is inside the subject as a determination result by the determination unit. An image signal is output to a display device, and the tip portion is inspected The second image signal of the second image, which is different from the display form of the first image from the detection signal, and has a smaller amount of image information regarding the subject than the first image signal. And an image generation circuit 25b that forms a signal processing unit that converts and outputs the signal to the display device.
Next, a typical operation of this embodiment will be described with reference to FIG. The surgeon connects the scanning endoscope 2 to the main body device 3, and turns on the power switch of the main body device 3 that is the power switch of the scanning endoscope apparatus 1.

Then, the controller 25 in the main body device 3 is in an operating state, and in step S1, the controller 25 reads ID data and the like from the memory 6 of the scanning endoscope 2 connected to the main body device 3. The ID data includes calibration data and table data, and the read ID data is stored in the memory 24 (and referred to in the operation described later).
As the next step S2, the surgeon adds a difference from the first image in the second image displayed on the monitor 4 when the distal end portion 11a is determined to be outside the patient 5 (or emphasizes the visual difference). Main display form (or display form item) is selected or designated from the input device 9. When selecting a main display form (item) for making a difference from the first image in the second image, the operator selects, for example, the following four display forms (items) from the input device 9.
a) Reduced display for reducing the size or angle of view of the second image compared to the first image;
b) Monochrome display that changes the second image to a monochrome image with respect to the color image of the first image;
c) Resolution / gradation reduction display in which the resolution or the number of gradations is reduced or deteriorated from the image quality of the first image,
d) Select an arbitrary one in the information superimposing display in which the information with the reduced laser light quantity is superimposed while the first image with the reduced laser light quantity is reduced from the state of the laser light quantity in the first image. can do. In this case, the input device 9 forms a display form (item) selection unit that selects or designates a main display form (item) for making a difference from the first image in the second image. Note that a plurality of items may be selected instead of one.

FIG. 7 shows an image display example displayed on the display area (display screen) 4a of the monitor 4 when the reduced display is selected. The left side of FIG. 7 shows the first image I1 when the distal end portion 11a is determined to be inside the patient 5, and when the distal end portion 11a is determined to be outside the patient 5, as shown on the right side, A second image I2 having an image size (or angle of view) reduced from the one image I1 is displayed. Note that the dotted line on the right side in FIG. 7 indicates the image size (or angle of view) of the first image I1. In FIG. 7, the first image I1 and the second image I2 are indicated by crossed oblique lines. For example, the second image generation circuit 52 performs a reduction process on the first image signal to generate a second image signal. As a reduction process in this case, for example, the second image signal may be generated by a thinning process that extracts every other pixel in the horizontal direction and the vertical direction in the first image. In this case, the image processing of the second image generation circuit 52 can be configured with a simple thinning circuit.
FIG. 8 shows an example of an image displayed on the display area (display screen) 4a of the monitor 4 when monochrome display is selected. The left side of FIG. 8 shows a color first image I1co when the distal end portion 11a is determined to be inside the patient 5. When it is determined that the distal end portion 11a is outside the patient 5, the second image generation circuit 52 performs image processing corresponding to a chroma killer on the first image signal and performs color processing as shown on the right side. A monochrome second image signal is generated for one image I1co. In FIG. 8, the color first image I1co is indicated by crossed diagonal lines, and the monochrome second image signal is indicated by diagonal lines.
A monochrome second image I2mo is displayed in the display area 4a. In addition to the monochrome image, a monochrome image such as red, green, or blue may be generated as the monochrome second image I2mo so that the monochrome image can be selected to be displayed in the display area 4a.

For example, the second image generation circuit 52 turns on / off a switch (not shown) so that only one color signal in the three primary color signals of R, G, B in the first image signal is output to the monitor 4. Also good. Even in this case, the second image generation circuit 52 can be realized by a switch switching circuit having a simple configuration.
FIG. 9 schematically shows an image display example displayed on the display area (display screen) 4a of the monitor 4 when the reduced resolution display is selected. The left side of FIG. 9 shows the first image I1co in color when the distal end portion 11a is determined to be inside the patient 5, and the right side shows the second image I2coa with the number of pixels reduced from that of the first image I1co. In FIG. 9, the color first image I1co is indicated by a diagonal line, and the second image I2coa is indicated by a crossed diagonal line that is coarser than the crossed diagonal line in the case of the first image I1co.
For example, when it is determined that the distal end portion 11a is outside the patient 5, the second image generation circuit 52 includes, for example, nine pixels (blocks) including, for example, three pixels adjacent to each other in the horizontal direction and the vertical direction in the first image I1co. ) Is processed as a unit pixel (block) of the second image.
In this case, the second image generation circuit 52 applies the pixel value that is the center of each of the nine pixels in the first image I1co to all eight surrounding pixels, so that all nine pixels have the same pixel value. The second image signal is converted or changed to the second image signal of the second image I2coa whose resolution is significantly deteriorated compared to the first image I1co. (For example, 16 pixels other than the above 9 pixels may be used, and the user may be able to select the degree of resolution reduction.)

Further, FIG. 9 is a schematic diagram that is also used in the case of the gradation number reduction display. When it is determined that the distal end portion 11a is outside the patient 5, the second image generation circuit 52 determines that the number of gradations (signal level) of the first image signal is, for example, 12 bits (within the range). The second image signal is converted into the second image signal of the second image I2coa, which is greatly reduced in the number of gradations compared to the first image I1co, or limited to, for example, 8 to 4 bits (within the range) reduced from the number of bits. change.
Then, as shown on the right side of FIG. 9, the display area 4a displays the second image I2coa having a lower number of gradations than the first image I1co.
FIG. 10 shows an image display example displayed on the display area (display screen) 4a of the monitor 4 when the information superimposition display is selected. The left side of FIG. 10 shows a first color image I1co when the distal end portion 11a is determined to be inside the patient 5, and when the distal end portion 11a is determined to be outside the patient 5, as shown on the right side thereof. The image in which the luminance level (signal level) is reduced in the first image I1co is changed to the second image I2cob, and information that explicitly indicates that the output of the laser beam has been reduced is, for example, weakened. The character information and symbol information are superimposed and displayed.
In FIG. 10, the signal level Sl in the image signal along the horizontal line passing through the center of the image is shown below the first image I1co and the second image I2cob. In the example, the signal level S1 of the second image I2coa is less than a fraction of the signal level S1 of the first image I1co.

The surgeon determines from the brightness of the image that the distal end portion 11a is inside, and is determined to be the first image I1co corresponding to a predetermined laser output or the distal end portion 11a is outside, It is possible to easily recognize or visually confirm whether the second image I2cob is obtained when the laser output is reduced to, for example, a fraction of the laser output.
Note that FIG. 10 shows an example in which information in which the output of the laser beam is weakened is displayed in a state of being superimposed on the image of the second image I2cob. In this case, the second image I2cob is an image having a smaller amount of image information related to the subject than the first image I1co due to the information superimposed on the second image I2cob.
In this way, information regarding the output of the laser beam is displayed on the image of the second image I2cob, and when it is displayed in the vicinity of the second image I2cob (not on the image of the second image I2cob). It may also be possible to select. When the latter selection is performed, information in which the output of the laser beam is weakened is displayed near or around the second image I2cob. In addition, although the 2nd image in any case of FIGS. 7-9 mentioned above turns into an image with little image information amount compared with a 1st image, since the 2nd image is not intending to observe the inside of a body, The switching of the output of the laser beam can be shown to the user without disturbing the observation inside the body.

As shown in FIG. 6, in step S <b> 3 next to the process of step S <b> 2, the controller 25 controls the drive unit 22 to apply a drive signal to the actuator 16. In step S4, the current detection circuits 37a and 37b detect the current I of the drive signal and output it to the determination circuit 25c.
In step S5, the determination circuit 25c calculates the resistance value Z of the piezoelectric elements 17a to 17d from the drive voltage V and the current I when the current I is detected. In the next step S6, the determination circuit 25c refers to the table data, and acquires the temperature T of the piezoelectric elements 17a to 17d from the resistance value Z from the table data.
In the next step S <b> 7, the determination circuit 25 c determines whether or not the distal end portion 11 a is inside the patient 5 based on whether or not the temperature T falls within the temperature range within the patient 5.
If it is determined that the distal end portion 11a is inside the patient 5, the controller 25 controls the drive unit 22 in the next step S8, and the drive unit 22 outputs a predetermined drive signal as shown in FIG. It controls to apply to.

In the next step S9, the controller 25 (the light source control circuit 25a) controls the laser light sources 31a to 31c of the light source unit 21, and the laser light sources 31a to 31c emit pulses at a predetermined timing and with a predetermined laser output. As will be described later, the laser output in this case becomes strong when the reduced laser output is weak (when it is determined that the distal end portion 11a is outside the patient 5).
In this case, the light receiving optical fiber 15 receives the return light reflected on the subject side irradiated with the laser light by pulse emission and guides it to the detection unit 23. The detection signal photoelectrically converted by the detection unit 23 is stored in the memory 44, and the first image generation circuit 51 generates an image signal corresponding to the spiral scan with reference to the calibration data.
In the next step S <b> 10, the first image generation circuit 51 performs raster conversion from the image signal corresponding to the spiral scan to generate a first image signal as an orthogonal coordinate system image signal, and outputs the first image signal to the monitor 4.
In the next step S11, the monitor 4 displays the subject image of the examination site inside the patient 5 as the first image.

In the next step S <b> 12, the controller 25 determines whether the surgeon has made a selection to determine whether the distal end portion 11 a is inside the patient 5 using the image. When selection using an image is performed, in the next step S12, the determination circuit 25c determines that the determination result of the temperature T acquired by the resistance value Z and the determination result by the image processing by the determination processing circuit 53 are both It is determined whether the part 11a is a determination result in the patient 5 or not.
If this determination result is met, the process returns to step S8 and the above-described process is repeated. On the other hand, if both the determination results are not internal (ie, external), the determination results are sent to the laser light sources 31a to 31c and the second image generation circuit 52, and the process proceeds to step S15.
If determination using an image is not selected in the determination processing in step S12, the determination circuit 25c determines in step S13 from the resistance value Z calculated by current detection by the current detection circuits 37a and 37b. The temperature T corresponding to the resistance value Z is acquired.

In step S <b> 15, the determination circuit 25 c determines whether the distal end portion 11 a is inside the patient 5. If this determination result is met, the process returns to step S8. On the other hand, if the determination result is not internal, the process proceeds to step S16.
In step S16, the drive unit 22 drives the actuator 16 with a predetermined drive signal as in step S8.
In the next step S17, the controller 25 (the light source control circuit 25a) reduces the laser outputs of the laser light sources 31a to 31c by the determination signal for reducing the output of the laser light based on the determination result from the determination circuit 25c, and the laser light source 31a. ˜31c emits pulses with reduced laser power.
As described above, if the level of a predetermined laser output in the case of the determination result in which the distal end portion 11a is inside the patient 5 is made strong, the laser light sources 31a to 31c emit pulses with a laser output that is considerably smaller than that level. .
The first image generation circuit 51 generates the first image signal by the return light when the pulsed light is emitted in the reduced laser output state. The first image signal is input to the second image generation circuit 52.

In step S18, the second image generation circuit 52 generates the second image signal having the display form selected in step S2 from the first image signal. Specifically, the second image signal of the selected display form is generated and output to the monitor 4 in each of those shown on the right side in FIGS.
In the next step S19, the monitor 4 displays the second image in the selected display form. The surgeon can easily recognize from the second image different from the first image displayed on the monitor 4 that the distal end portion 11a is determined to be outside the body and the output of the laser light has been reduced.
In the next step S20, the determination circuit 25c determines whether or not the distal end portion 11a is outside the patient 5. Note that, as the determination processing in step S20, it may be determined whether or not the distal end portion 11a is outside the patient 5 by using both the image and the calculation of the resistance value Z (or acquisition of the temperature T). Then, it may be determined whether or not the distal end portion 11a is outside the patient 5 based on information on the calculation of the resistance value Z (or acquisition of the temperature T).
If the determination result is not external (ie, the internal determination result) in step S20, the process proceeds to step S8. On the other hand, if the determination result is external in step S20, the process proceeds to the next step S21.
In the next step S21, the controller 25 determines whether or not the operator has operated the input device 9 to input an instruction to end the endoscopic examination, and if the instruction to end the examination has not been input. The process returns to step S16. On the other hand, when the instruction input for ending the speculum inspection is performed, the processing in FIG. 6 is ended.

According to this embodiment that operates in this manner, when the distal end portion 11a of the scanning endoscope 2 is outside the body, the distal end portion 11a of the scanning endoscope 2 is covered by an image displayed on the display device. The user can easily recognize or confirm that it is outside the sample.
That is, when the distal end portion 11a is actually pulled out of the body, by observing a change in the image displayed on the display device (change from the first image to the second image), the laser light as the illumination light is observed. It is easy to check whether the output has been reduced.
In addition, when the distal end portion 11a is actually pulled out of the body, if the first image remains as it is and does not change to the second image due to an erroneous determination, a user such as an operator who performs the operation observes It is possible to quickly recognize that the output of the laser beam is strong due to the erroneous determination from the captured image, and to reduce the output of the laser beam or to take care not to irradiate other users etc. with the laser beam It becomes easy to perform such operations quickly. That is, it becomes easy to quickly perform operations and measures for erroneous determination.
In the process shown in FIG. 6, after the step (for example, steps S14, S15, S20) in which it is determined that the distal end portion 11a is inside, the user outputs the laser beam from the input device 9 within an appropriate time. An instruction operation to be reduced may be received, and a control operation corresponding to the received instruction operation may be performed.
In this case, in the case of an image that results in a laser output with the internal determination result in spite of the leading end portion 11a being pulled out due to an erroneous determination, the user uses the input device 9 to perform laser output. An instruction operation for reducing the light output is performed, the laser light output is reduced, and the user can be protected smoothly when the tip portion 11a is pulled out.
In addition, according to the present embodiment, the user can select display form items such as resolution so that the visual difference between the second image and the first image becomes significant. It is easier for the user to confirm the second image when it has changed (than when it cannot be selected).
Further, in the present embodiment, the characteristic that the resistance value Z of the piezoelectric elements 17a to 17d constituting the actuator 16 shows temperature dependence is utilized without arranging a temperature sensor for detecting the temperature inside the tip end portion 11a. Thus, it is possible to determine whether the distal end portion 11a is inside or outside the patient 5. For this reason, according to this embodiment, it is easy to reduce the diameter of the insertion portion 11 of the scanning endoscope 2 (suitable for reducing the diameter).

In the above-described embodiment, the case where the two current detection circuits 37a and 37b are provided has been described. However, a configuration in which one current detection circuit 37a or 37b is provided may be employed. For example, the combined resistance value of the piezoelectric elements 17a and 17b or the resistance value of one of the piezoelectric elements 17a and 17b may be calculated by one current detection circuit 37a.
In addition, since a predetermined drive signal is repeatedly applied to the piezoelectric elements 17a to 17d, the piezoelectric elements 17a to 17d are heated in such an applied state as compared to a state in which the piezoelectric elements 17a to 17d are not applied. Become.
For this reason, table data is generated in consideration of such an applied state, or the temperature T acquired from the resistance value Z of the piezoelectric element and whether the temperature T falls within the temperature range inside the patient 5 or not. A range may be set. Further, the temperature range may be variably set according to the examination site where the distal end portion 11a is inserted into the patient 5.
Further, as in the modification shown in FIG. 11, a configuration in which a user such as an operator is provided with a front switch 56 serving as a forced switching switch that can be used only when required by the user's judgment. Then, the light amount of the laser light of the laser module 31d may be forcibly switched from strong to weak by a manual instruction operation by the user.

The front switch 56 serving as a forced switching switch is a manually operated switch that can be used only in the case of a determination result in which the distal end portion 11a is inside the patient 5.
For this reason, in the state before the front switch 56 is operated, the light source control circuit 25a in the FPGA 30 (or the controller 25) outputs a laser strong signal to the laser module 31d, and the laser module 31d becomes strong. In this state, the amount of laser light is emitted to the illumination optical fiber 13b side.
Further, in conjunction with the control state of the light source control circuit 25a, the image generation circuit 25b is in a state of outputting the first image signal generated by the first image generation circuit 51 to the monitor 4.
In such a state, when the user performs an instruction operation to weaken (from strong) the front switch 56, the FPGA 30 (or the controller 25) sends the instruction operation signal in the FPGA 30 (or the controller 25). The light source control circuit 25a outputs the laser weak signal to the laser module 31d, and the laser module 31d emits the light amount of the weakened laser light to the illumination optical fiber 13b side.
The instruction operation signal is sent to the image generation circuit 25b in conjunction with the control of the light source control circuit 25a. Then, the second image generation circuit 52 in the image generation circuit 25 b outputs the second image signal generated from the first image generation circuit 51 to the monitor 4.

In FIG. 11, the front switch 56 is shown as a manual switching switch for manual operation. However, a foot switch or an operation switch provided near the rear end of the insertion portion 11 of the scanning endoscope 2 may be used. Alternatively, when an operation unit is provided at the rear end of the insertion unit 11, an operation unit switch provided in the operation unit may be used.
In FIG. 11, when the input device 9 is used to switch the laser light quantity by the front switch 56, FIG. 11 has the same configuration as FIG.
According to this modification, in addition to the effects of the first embodiment, the laser light quantity can be switched so that the user can be protected only when the user needs to be protected (need to protect the user). In the case where the tip portion 11a is outside, the amount of laser light is already weak, and there is little need for an operation to make it weaker).
Further, after inserting the patient 5 into the body and performing an endoscopic examination, in the case where the insertion portion 11 is pulled out from the body, the amount of laser light remains strong, The operation for forcibly reducing the amount of laser light and protecting the user can be performed.

In addition, the present invention is not limited to the above-described configuration, and for example, an acceleration sensor 61 may be provided inside the distal end portion 11a in FIG. 1 as indicated by a two-dot chain line. Then, an acceleration detection signal from the acceleration sensor 61 is input to the determination circuit 25c via the signal line 62, and the determination circuit 25c determines whether the distal end portion 11a is inside the patient 5 based on the acceleration detection signal. You may make it determine whether it exists in.
The acceleration sensor 61 is at least biaxial, for example, an acceleration acting in the longitudinal direction of the distal end portion 11a and a direction orthogonal to the longitudinal direction and in which the piezoelectric elements 17a and 17b vibrate or a direction in which the piezoelectric elements 17a and 17b vibrate. The acceleration of is detected.
For example, when the state in which the acceleration acting in the longitudinal direction coincides with the gravity component and the average value of the acceleration in the direction orthogonal to the longitudinal direction is almost zero continues for a predetermined time or longer, the determination circuit 25c Is pulled out of the patient 5 and hung on a hanger (that is, a state in which the acceleration acting in the longitudinal direction of the insertion portion 11 (the distal end portion 11a thereof coincides with the gravity component acting in the vertical direction)), You may make it determine with the front-end | tip part 11a being the exterior (the patient 5). Further, a sensor for detecting the angle of the vibration center of the distal end portion 11a with respect to the vertical direction is provided, and the determination circuit 25c determines whether the distal end portion 11a is inside or outside the patient 5 based on the output of the sensor. May be.
In the above-described embodiment, a configuration including the second image generation circuit 52 that generates the second image having a different display form may be regarded as a different embodiment.

DESCRIPTION OF SYMBOLS 1 ... Scanning endoscope apparatus, 2 ... Scanning endoscope, 3 ... Main body apparatus, 4 ... Monitor, 5 ... Patient, 6 ... Memory, 7 ... Connector, 9 ... Input device, 11 ... Insertion part, 11a ... Tip portion, 13 ... lighting optical fiber, 15 ... light receiving optical fiber, 16 ... actuator, 17a to 17d ... piezoelectric element, 21 ... light source unit, 22 ... drive unit, 23 ... detection unit, 24 ... memory, 25 ... controller , 25a ... light source control circuit, 25b ... image generation circuit, 25c ... determination circuit, 30 ... FPGA, 31a-31c ... laser light source, 33 ... signal generator, 35a, 35b ... amplifier, 37a, 37b ... current detection circuit, 37 ... detector, 42 ... patient circuit, 51 ... first image generation circuit, 52 ... second image generation circuit, 53 ... determination processing circuit,

Claims (10)

A fiber having a first end where incident light is incident and a second end that emits the illumination light toward the subject; a scanning unit that vibrates the second end so as to form a spiral trajectory; A scanning endoscope comprising:
A detection element that detects reflected light from the subject side and outputs a detection signal;
A determination unit that determines whether the distal end portion of the scanning endoscope in which the second end portion is disposed is inside or outside the subject;
As a result of determination by the determination unit, when the tip is inside the subject, the first image signal of the first image generated from the detection signal is output to a display device, and the tip is the subject. The second image signal of the second image, which is different from the display form of the first image from the detection signal, and has a smaller amount of image information regarding the subject than the first image signal. A signal processing unit for converting and outputting to the display device;
A scanning endoscope apparatus comprising:   2. The scanning endoscope according to claim 1, wherein the signal processing unit converts the second image signal into display information indicating that the second image is outside the subject. apparatus.   The scanning endoscope apparatus according to claim 1, wherein the signal processing unit superimposes information related to the determination result on the second image and converts the information into the second image signal.   The signal processing unit converts the second image into an image having a resolution smaller than that of the first image, a gradation number smaller than that of the first image, or an angle of view smaller than that of the first image. The scanning endoscope apparatus according to claim 1.   The illumination light control circuit further accepts a user input only when the determination result by the determination unit is inside the subject, and lowers the intensity of the illumination light according to the user input. The scanning endoscope apparatus according to 1.   The scanning endoscope apparatus according to claim 1, wherein the determination unit outputs information of the determination result based on the first image signal. The determination unit includes a sensor that detects a temperature around the tip, or an angle of a vibration center of the tip with respect to a vertical direction,
The scanning endoscope apparatus according to claim 6, wherein the signal processing unit outputs information on the determination result based on the first image signal and the output of the sensor. And a light source unit that generates the illumination light incident on the first end of the fiber;
A light amount control unit that controls the light amount of the illumination light generated by the light source unit to at least a first light amount and a second light amount that is ½ or less of the first light amount;
The first signal corresponding to a subject image inside or outside the subject is detected from the detection signal provided in the signal processing unit and based on return light from inside or outside the subject irradiated with the illumination light. A first image generation circuit for generating an image signal;
A first processing unit configured to generate the second image signal of the second image having a display form different from that of the first image, the luminance level of the first image being at least small from the first image signal; A two-image generation circuit;
Have
The light amount control unit is configured to change a light amount incident on the first end portion of the fiber from the first light amount to the second light amount based on a determination result by the determination unit that the tip portion is outside the subject. Control to reduce the amount of light,
The second image generation circuit generates the first image signal from the first image signal for the display device from which the first image signal was output in conjunction with the control of the light amount control unit to reduce the second light amount. The scanning endoscope apparatus according to claim 1, wherein the second image signal is output to the display device. Further, the second image displayed on the display device includes a selection unit that selects at least one of a plurality of display form items including a resolution and an angle of view at which a difference from the first image appears.
9. The scanning type according to claim 8, wherein the second image generation circuit performs an image conversion process on the first image signal so as to generate the second image corresponding to the selected display form item. Endoscopic device. The scanning endoscope apparatus according to claim 8, wherein the light source unit generates laser light as the illumination light.

Images