Endoscope device and endoscope system

Abstract

The endoscope apparatus (5) includes: a light source unit (13) capable of switching the spectral distribution of illumination light; an imaging element (27) that acquires an image by receiving the reflected light of the illumination light; an image processing unit (19) that determines whether a field-of-view defect caused by stone fragments has occurred within the field of view of the imaging element (27), the stone fragments being the fragments of a stone that has been broken by irradiating a laser from a laser pulse generation device (3); and a light source control unit (31) that controls the light source unit (13) based on the determination result of the image processing unit (19). When the image processing unit (19) determines that no field-of-view defect has occurred, the light source control unit (31) causes white light illumination light to be emitted from the light source unit (13). When it is determined that a field-of-view defect has occurred, the light source control unit (31) switches the illumination light emitted from the light source unit (13) to light in the blue region.

Description

Technical Field

[0001] The present invention relates to an endoscope device and an endoscope system. Background Art

[0002] In recent years, in transurethral lithotripsy (TUL) based on a pyeloureteroscope, a procedure called pulverization in which stones are broken into fine stones has attracted attention. Pulverization enables the stones to be discharged out of the body together with the perfusion fluid. On the other hand, the illumination light is scattered by the stone fragments flying during the pulverization, and thus the field of view of the endoscope deteriorates.

[0003] Conventionally, as a technique for performing pulverization while ensuring the field of view, the following endoscope device is known: a channel for discharging a liquid is provided separately from a channel for emitting illumination light, and by increasing the perfusion flow rate, the stone fragments are efficiently discharged out of the body (for example, refer to Non-Patent Document 1).

[0004] Prior Art Documents

[0005] Non-Patent Documents

[0006] Non-Patent Document 1: Haberman, Ken, et al. "A dual-channel flexible ureteroscope: evaluation of deflection, flow, illumination, and optics." Journal of endourology 25.9 (2011): 1411-1414. Summary of the Invention

[0007] Problems to be Solved by the Invention

[0008] However, if the perfusion flow rate is increased to ensure the field of view, there are the following disadvantages: the pressure in the renal pelvis rises, and the risk of complications such as sepsis increases.

[0009] The present invention has been made in view of the above circumstances, and an object thereof is to provide an endoscope device and an endoscope system that can ensure the field of view with a simple operation without increasing the perfusion flow rate.

[0010] Means for Solving the Problems

[0011] In order to achieve the above object, the present invention provides the following means.

[0012] A first aspect of the present invention is an endoscope device having: a light source capable of switching the spectral distribution of illumination light; an imaging unit that acquires an image by receiving the reflected light of the illumination light; a determination unit that determines whether a field-of-view defect caused by stone fragments has occurred within the field of view of the imaging unit, the stone fragments being stone fragments broken by irradiating a laser from a laser pulse generation device; and a control unit that controls the light source based on the determination result of the determination unit. When it is determined by the determination unit that the field-of-view defect has not occurred, the control unit emits the illumination light of white light from the light source. When it is determined that the field-of-view defect has occurred, the control unit switches the illumination light emitted from the light source to light in the blue region.

[0013] According to this aspect, illumination light is irradiated onto the observation area by the light source, and an image of the observation area is acquired by the imaging unit.

[0014] When a stone is broken by a laser pulse generation device, if the illumination light is scattered by the stone fragments, the field of view of the imaging unit deteriorates. For example, when the illumination light is reflected and scattered by relatively large stone fragments visible to the naked eye, multiple bright spots appear in the image. In addition, when the illumination light is backscattered by Mie scattering due to fine stone fragments that are not visible to the naked eye, the image appears cloudy.

[0015] Stones are usually mostly brown or yellow, and as the spectral reflectance, the reflectance of light in the blue region is low. In addition, when the wavelength of the illumination light is shorter than the diameter of the stone fragments, the intensity of the backscattering based on Mie scattering becomes weaker. Therefore, when a field-of-view defect caused by stone fragments occurs, it is preferable to observe using illumination light in the blue region with a low reflectance and backscattering intensity from the stone fragments. On the other hand, the light in the blue region changes the hue of the image. Therefore, when no field-of-view defect occurs, it is preferable to observe using white light.

[0016] Therefore, when it is determined by the determination unit that no field-of-view defect caused by stone fragments has occurred within the field of view of the imaging unit, the control unit emits the illumination light of white light from the light source. When it is determined that the field-of-view defect has occurred, the control unit emits the illumination light in the blue region from the light source. Thus, the hue of the image can be ensured during normal observation, and when a field-of-view defect is caused by stone fragments, the field of view can be ensured by a simple operation without increasing the irrigation flow rate.

[0017] In the above aspect, it may also be that the light in the blue region is light having a strongest wavelength of 500 nm or less.

[0018] In the above method, it may also be that the determination unit determines whether the field of view defect has occurred based on a parameter related to the amount of high-frequency components in the image that are higher than a specified frequency. Additionally, the parameter may also be a spectral component.

[0019] When small bright spots appear in the image due to stone fragments, the brightness signal waveform of the image is a waveform with high-frequency noise. Therefore, based on a parameter related to the amount of high-frequency components in the image, it is possible to determine the field of view defect.

[0020] In the above method, it may also be that the endoscope device has a calculation unit that calculates the ratio of the cumulative value of the spectral components higher than the specified frequency to the cumulative value of the spectral components lower than the specified frequency. When the ratio calculated by the calculation unit is greater than the specified threshold, the determination unit determines that the field of view defect has occurred.

[0021] By using the calculation unit to obtain the ratio of the cumulative value of the spectral components on the high-frequency side to the cumulative value of the spectral components on the low-frequency side, it can be known whether there are more high-frequency components or more low-frequency components in the image. Additionally, when there are more high-frequency components in the image, a field of view defect will occur. Therefore, by comparing the ratio calculated by the calculation unit with the specified threshold, it is possible to accurately determine whether the field of view defect has occurred.

[0022] In the above method, it may also be that the determination unit determines whether the field of view defect has occurred based on the oscillation conditions of the laser emitted by the laser pulse generating device.

[0023] The size of the stone fragments when the stone is broken by the laser varies according to the oscillation conditions such as the output and pulse width of the irradiated laser. And depending on the size of the stone fragments, the possibility of the image looking cloudy is different. Therefore, based on the oscillation conditions of the laser, it is possible to determine the field of view defect.

[0024] In the above method, it may also be that when the oscillation conditions satisfy all of the following conditional expressions (1) to (3), the determination unit determines that the field of view defect has occurred:

[0025] The wavelength of the laser is 1900 nm to 3000 nm (1)

[0026] The energy of the laser is 200 mJ to 400 mJ (2)

[0027] The frequency of the laser is 50 Hz to 80 Hz (3).

[0028] If the oscillation conditions of the laser satisfy all of the conditional expressions (1) to (3), the calculus can be broken into relatively small particulate form. Also, in this case, the illumination light is backscattered due to Mie scattering, and thus the image is likely to appear cloudy. Therefore, it is possible to highly accurately determine whether a poor field of view has occurred based on whether the oscillation conditions of the laser emitted from the laser pulse generation device satisfy all of the conditional expressions (1) to (3).

[0029] In the above-described aspect, it may also be that the light source includes a xenon lamp and an interference filter disposed in a pluggable manner in the optical path of the illumination light emitted from the xenon lamp, and the control unit switches the spectral distribution of the illumination light by plugging and unplugging the interference filter with respect to the optical path of the illumination light.

[0030] In a configuration using a xenon lamp, by the control unit, by simply switching the plugging and unplugging of the interference filter during normal observation and when a poor field of view occurs, it is possible to irradiate illumination light of white light during normal observation and illumination light in the blue region when a poor field of view occurs.

[0031] In the above-described aspect, it may also be that the light source includes a plurality of LED light sources that emit light of different colors, and the control unit switches the spectral distribution of the illumination light by changing the LED light source to be driven.

[0032] According to this configuration, by the control unit, by simply changing the LED light source that emits light during normal observation and when a poor field of view occurs, it is possible to irradiate illumination light of white light during normal observation and illumination light in the blue region when a poor field of view occurs.

[0033] In the above-described aspect, it may also be that the light source includes an LED light source and an optical filter disposed in a pluggable manner in the optical path of the illumination light emitted from the LED light source, and the control unit switches the spectral distribution of the illumination light by plugging and unplugging the optical filter with respect to the optical path of the illumination light.

[0034] In a configuration using an LED light source, by the control unit, by simply switching the plugging and unplugging of the optical filter during normal observation and when a poor field of view occurs, it is possible to irradiate illumination light of white light during normal observation and illumination light in the blue region when a poor field of view occurs.

[0035] A second aspect of the present invention is an endoscope system including: a laser pulse generation device that irradiates a calculus with a laser; and any one of the above-described endoscope devices.

[0036] In the above-described aspect, it may also be that the light in the blue region is light having a wavelength of 500 nm or less with the strongest intensity.

[0037] In the above method, it is also possible that the determination unit determines whether the field of view defect has occurred based on a parameter related to the amount of high-frequency components in the image that are higher than a specified frequency.

[0038] In the above method, the parameter may also be a spectral component.

[0039] In the above method, it is also possible that the endoscope device has a calculation unit that calculates the ratio of the cumulative value of the spectral components higher than the specified frequency to the cumulative value of the spectral components lower than the specified frequency. When the ratio calculated by the calculation unit is greater than the specified threshold, the determination unit determines that the field of view defect has occurred.

[0040] In the above method, it is also possible that the determination unit determines whether the field of view defect has occurred based on the oscillation conditions of the laser emitted by the laser pulse generation device.

[0041] In the above method, it is also possible that when the oscillation conditions satisfy all of the following conditional expressions (1) to (3), the determination unit determines that the field of view defect has occurred:

[0042] The wavelength of the laser is 1900 nm to 3000 nm (1)

[0043] The energy of the laser is 200 mJ to 400 mJ (2)

[0044] The frequency of the laser is 50 Hz to 80 Hz (3).

[0045] In the above method, it is also possible that the light source includes: a xenon lamp; and an interference filter disposed in the optical path of the illumination light emitted from the xenon lamp in a pluggable manner. The control unit switches the spectral distribution of the illumination light by plugging and unplugging the interference filter with respect to the optical path of the illumination light.

[0046] In the above method, it is also possible that the light source includes a plurality of LED light sources that emit light of different colors. The control unit switches the spectral distribution of the illumination light by changing the LED light source to be driven.

[0047] In the above method, it is also possible that the light source includes an LED light source and an optical filter disposed in the optical path of the illumination light emitted from the LED light source in a pluggable manner. The control unit switches the spectral distribution of the illumination light by plugging and unplugging the optical filter with respect to the optical path of the illumination light.

[0048] Advantages of the Invention

[0049] According to the present invention, an effect of ensuring a field of view with a simple operation without increasing the irrigation flow rate is obtained. BRIEF DESCRIPTION OF THE DRAWINGS

[0050] Figure 1 is an overall configuration diagram of an endoscope system according to a first embodiment of the present invention.

[0051] Figure 2 is a diagram showing a region of a frequency of 52 cyc / L in an FFT image.

[0052] Figure 3 is showing by Figure 1 An example of a spectral distribution of illumination light irradiated by the endoscope device when a poor field of view occurs.

[0053] Figure 4 is an example of an endoscope image when a poor field of view occurs.

[0054] Figure 5 is an overall configuration diagram of an endoscope system according to a modified example of the first embodiment of the present invention.

[0055] Figure 6 is showing by Figure 5 An example of a spectral distribution of illumination light irradiated by the endoscope device when a poor field of view occurs.

[0056] Figure 7 is an overall configuration diagram of an endoscope system according to a second embodiment of the present invention.

[0057] Figure 8 is an overall configuration diagram of an endoscope system according to a modified example of the second embodiment of the present invention. DETAILED DESCRIPTION OF THE INVENTION

[0058] [First Embodiment]

[0059] Hereinafter, an endoscope device and an endoscope system according to a first embodiment of the present invention will be described with reference to the drawings.

[0060] As Figure 1 shown, the endoscope system 1 according to the present embodiment includes a laser pulse generation device 3 for treating urinary tract stones and the like, and an endoscope device 5 for observing an observation region in a patient's body cavity.

[0061] The laser pulse generating device 3 breaks up a calculus by irradiating the calculus in the body cavity of a patient with a laser. The laser pulse generating device 3 includes: a laser oscillator 7 that oscillates a laser; and a laser guiding member 9 that guides the laser emitted from the laser oscillator 7 to the body cavity of the patient. The laser oscillator 7 can change the laser pulse width and can break the calculus into larger fragments (Fragmentation) or finely break the calculus into a granular form (Dusting).

[0062] The endoscope device 5 has: a long and slender flexible insertion portion 11 that is inserted into the body of the patient; a light source unit (light source) 13 that generates illumination light; an illumination unit 15 that irradiates the observation area with the illumination light emitted from the light source unit 13; an imaging unit 17 that acquires image information of the observation area irradiated with the illumination light; and an image processing unit (determination unit, calculation unit) 19 that processes the image information acquired by the imaging unit 17. The endoscope device 5 is connected to a monitor (not shown) that displays an endoscope image (image) generated by the image processing unit 19.

[0063] The illumination unit 15 has: an optical fiber 21 that is arranged along the longitudinal direction within the insertion portion 11; and an illumination optical system 23 that is arranged at the distal end 11a of the insertion portion 11.

[0064] The optical fiber 21 guides the illumination light emitted from the light source unit 13 from the proximal end of the insertion portion 11 to the vicinity of the distal end 11a.

[0065] The illumination optical system 23 irradiates the illumination light emitted from the distal end of the optical fiber 21 onto the observation area facing the distal end 11a of the insertion portion 11.

[0066] The imaging unit 17 is arranged near the distal end 11a of the insertion portion 11. The imaging unit 17 has: an objective lens 25 that converges the return light (reflected light) returning from the observation area irradiated with the illumination light; and an imaging element (imaging portion) 27 such as a CCD (Charge Coupled Device) that captures the return light converged by the objective lens 25. The image information acquired by the imaging element 27 is transmitted to the image processing unit 19.

[0067] A channel 11b that penetrates in the longitudinal direction of the insertion portion 11 is provided in the insertion portion 11. The laser guiding member 9 of the laser pulse generating device 3 is inserted through the channel 11b. The laser guiding member 9 passes through the channel 11b and protrudes from the distal end 11a of the insertion portion 11 and is arranged at a position facing the calculus in the body cavity. The laser transmitted from the laser oscillator 7 by the laser guiding member 9 is irradiated onto the calculus.

[0068] In addition, in order to ensure the field of view of the endoscope device 5, the channel 11b is also used for the purpose of delivering the perfusion fluid. The proximal end of the channel 11b is connected to a liquid delivery unit such as a syringe or a pump (not shown). The liquid delivery unit discharges the perfusion fluid from the front end 11a of the insertion portion 11 via the channel 11b.

[0069] The image processing unit 19 generates an endoscope image of the observation area based on the image information transmitted from the imaging element 27. In addition, the image processing unit 19 determines whether there is a poor field of view in the field of view of the imaging element 27 due to the fragments of the stone broken by the laser pulse generating device 3, that is, the stone fragments.

[0070] For example, the image processing unit 19 determines whether there is a poor field of view caused by stone fragments based on a parameter related to the amount of high-frequency components higher than a specified frequency in the endoscope image obtained by the imaging element 27. Hereinafter, a method for determining whether the field of view is poor performed by the image processing unit 19 will be described in detail.

[0071] The image processing unit 19 performs a Fourier transform on the luminance signal of the generated endoscope image, and calculates the ratio of the cumulative value of the spectral components on the high-frequency side to the specified threshold and the cumulative value of the spectral components on the low-frequency side to the specified threshold. Thus, it is known whether there are more high-frequency components or low-frequency components in the endoscope image. When there are more high-frequency components, the field of view of the imaging element 27 is blurred.

[0072] Let the length (number of pixels) of the horizontal opposite sides of the endoscope image be L, let the cumulative value of the spectral components less than the specified threshold be Sl, and let the cumulative value of the spectral components equal to or higher than the specified threshold be Sh. When Sh / Sl≥20, the image processing unit 19 determines that there are more high-frequency components in the endoscope image and there is a poor field of view caused by stone fragments. When Sh / Sl<20, the image processing unit 19 determines that there are more low-frequency components in the endoscope image and there is no poor field of view caused by stone fragments. As the specified threshold, for example, a value obtained from experiments, that is, a frequency of 52 cyc / L, is used. Figure 2 is an example of an FFT image (Fast Fourier Transform image). In Figure 2 the area surrounded by the quadrilateral frame represents the area of the frequency 52 cyc / L.

[0073] The light source unit 13 includes an LED light source 29 capable of changing the color of the emitted light and a light source control unit 31 that controls the LED light source 29.

[0074] The LED light source 29 includes a B-LED 33B having a peak intensity in the blue wavelength region, a G-LED 33G having a peak intensity in the green wavelength region, and an R-LED 33R having a peak intensity in the red wavelength region.

[0075] In addition, the light source unit 13 includes: a reflecting mirror 35 and dichroic mirrors 37A and 37B that synthesize white light illumination light by combining the illumination light emitted from each of the LEDs 33B, 33G, and 33R; and a converging lens 39 that converges the synthesized white light illumination light onto the incident end of the optical fiber 21 and causes it to enter the optical fiber 21.

[0076] The determination result of the image processing unit 19 is input to the light source control unit 31. The light source control unit 31 switches the spectral distribution of the illumination light generated from the light source unit 13 by controlling the outputs of the respective LEDs 33B, 33G, and 33R. Specifically, when the light source control unit 31 is input with the determination result of no field-of-view defect caused by stone fragments from the image processing unit 19, it drives the respective LEDs 33B, 33G, and 33R to emit white light illumination light from the light source unit 13.

[0077] On the other hand, when the light source control unit 31 is input with the determination result of a field-of-view defect caused by stone fragments from the image processing unit 19, it increases the emission light amount of the B-LED 33B, and on the other hand, decreases the emission light amounts of the G-LED 33G and the R-LED 33R, thereby switching the illumination light emitted from the light source unit 13 to light in the blue region. When the emission light amount of the B-LED 33B is increased while the emission light amount of the G-LED 33G is decreased and the R-LED 33R is not driven, for example, as Figure 3 shown, light in the blue region with the strongest intensity and a wavelength of 500 nm or less is emitted from the light source unit 13. In Figure 3 , the vertical axis represents the intensity (A.U.) of the illumination light, and the horizontal axis represents the wavelength (nm) of the illumination light. The same applies to Figure 6 .

[0078] The image processing unit 19 and the light source control unit 31 are implemented by at least one processor and a storage device having hardware. That is, an image processing program and a light source control program are stored in the storage device. And, by the processor, the above processing of the image processing unit 19 is executed according to the image processing program, and the above control of the respective LEDs 33B, 33G, and 33R by the light source control unit 31 is executed according to the light source control program. The image processing unit 19 and the light source control unit 31 may each include a processor and a storage unit.

[0079] Next, the operation of the endoscope system 1 of the present embodiment will be described below.

[0080] When using the endoscope system 1 of the present embodiment for treating, for example, urinary tract stones, first, the insertion portion 11 is inserted into the ureter from the ureteral orifice in the patient's bladder, and the light source control unit 31 causes the illumination light of white light to be emitted from the light source unit 13. At this time, through the liquid supply unit, the perfusion liquid for ensuring the field of view of the endoscope device 5 is discharged from the distal end 11a of the insertion portion 11.

[0081] The illumination light emitted from the light source unit 13 is guided by the optical fiber 21 to the vicinity of the distal end 11a of the insertion portion 11. And the illumination light emitted from the distal end of the optical fiber 21 is irradiated onto the observation region in the ureter that faces the distal end 11a of the insertion portion 11 through the illumination optical system 23.

[0082] The return light that returns from the observation region in the ureter by irradiating the illumination light of white light is converged by the objective lens 25 and then photographed by the imaging element 27. Thus, the image information of the observation region in the ureter is obtained by the imaging element 27, and the endoscope image in the ureter is generated by the image processing unit 19. The generated endoscope image is displayed on the monitor.

[0083] Next, while observing the endoscope image displayed on the monitor, the operator places the laser guide 9 opposite to the stone in the ureter. And the laser pulse generating device 3 is driven to irradiate the laser onto the stone, thereby crushing the stone.

[0084] Here, when the illumination light of the endoscope device 5 is scattered by the stone fragments, for example, as Figure 4 shown, the field of view of the imaging element 27 deteriorates. For example, when the illumination light is reflected and scattered by relatively large stone fragments visible to the naked eye, multiple flashing bright spots are generated in the endoscope image. In addition, when the illumination light is backscattered (the scattering in the forward direction of the light is stronger than that in the backward direction) by Mie scattering due to fine stone fragments that are not visible to the naked eye, the endoscope image looks cloudy.

[0085] Stones are usually mostly brown or yellow, and as the spectral reflectance, the reflectance of light in the blue region is low. In addition, when the wavelength of the illumination light is shorter than the diameter of the stone fragments, the intensity of the backscattering based on Mie scattering becomes weaker. Therefore, when the field of view deteriorates due to stone fragments, it is preferable to observe through the illumination light in the blue region with a low reflectance and backscattering intensity from the stone fragments. On the other hand, the light in the blue region changes the hue of the endoscope image, so in the case of normal observation when there is no deterioration of the field of view due to stone fragments, it is preferable to observe through white light.

[0086] In the endoscope apparatus 5, the image processing unit 19 determines whether a poor field of view is caused by stone fragments broken by the laser pulse generation device 3 within the field of view of the imaging element 27. Specifically, the image processing unit 19 calculates the ratio of the cumulative value Sl of the spectral components with a frequency less than 52 cyc / L to the cumulative value Sh of the spectral components with a frequency of 52 cyc / L or more in the cumulative value of the spectral components of the luminance signal of the endoscope image generated. And, by the image processing unit 19, when Sh / Sl≥20, it is determined that the field of view is poor, and when Sh / Sl<20, it is determined that no poor field of view has occurred.

[0087] When the image processing unit 19 determines that no poor field of view caused by stone fragments has occurred within the field of view of the imaging element 27, the light source control unit 31 continuously emits white light illumination light from the light source unit 13. Thereby, the color tone of the endoscope image can be ensured.

[0088] On the other hand, when the image processing unit 19 determines that a poor field of view caused by stone fragments has occurred within the field of view of the imaging element 27, the light source control unit 31 switches the illumination light emitted from the light source unit 13 to light in the blue region. Thereby, the poor field of view caused by stone fragments is suppressed, and the field of view of the endoscope apparatus 5 is ensured.

[0089] As described above, according to the endoscope system 1 of the present embodiment, the image processing unit 19 determines whether a poor field of view caused by stone fragments has occurred within the field of view of the imaging element 27. When it is determined that a poor field of view has occurred, the light source control unit 31 automatically switches the illumination light emitted from the light source unit 13 from white light illumination light to light in the blue region. Thereby, in the case of normal observation when no poor field of view caused by stone fragments has occurred, the color tone of the endoscope image can be ensured. In addition, when a poor field of view caused by stone fragments occurs, the field of view can be ensured by a simple operation without increasing the irrigation flow rate.

[0090] The present embodiment can be modified into the following structure.

[0091] In the present embodiment, the light source unit 13 includes a plurality of LEDs 33B, 33G, 33R, and the output of each LED 33B, 33G, 33R is controlled by the light source control unit 31. Instead, for example, as Figure 5 shown, the light source unit 13 includes a xenon lamp (Xe lamp) 41 and an interference filter 43 disposed in the optical path of the illumination light emitted from the xenon lamp 41 in a pluggable manner.

[0092] In addition, the light source unit 13 may be provided with a spectral control unit (control unit) 45 that controls the insertion and extraction of the interference filter 43 instead of the light source control unit 31. Further, the spectral control unit 45 may also switch the spectral distribution of the illumination light by inserting and extracting the interference filter 43 with respect to the optical path of the illumination light emitted from the xenon lamp 41.

[0093] The determination result of the image processing unit 19 is input to the spectral control unit 45. The spectral control unit 45 may also be implemented by the above-described processor and storage device. That is, a spectral control program may be stored in the storage device. Further, the above control of the spectral control unit 45 may be executed by the processor according to the spectral control program. The spectral control unit 45 may also include a processor and a storage unit.

[0094] As the interference filter 43, for example, a band-pass filter having a characteristic of cutting off wavelengths in regions other than the blue region is used. When the interference filter 43 is inserted into the optical path of the illumination light emitted from the xenon lamp 41, for example, as Figure 6 shown, light in the blue region with the strongest intensity and a wavelength of 500 nm or less is emitted from the light source unit 13.

[0095] When it is determined by the image processing unit 19 that there is no field-of-view defect caused by calculus fragments in the field of view of the imaging element 27, the interference filter 43 is detached from the optical path of the illumination light by the spectral control unit 45. Thus, the white light illumination light emitted from the xenon lamp 41 is directly emitted from the light source unit 13 and irradiated onto the observation region.

[0096] On the other hand, when it is determined by the image processing unit 19 that there is a field-of-view defect caused by calculus fragments in the field of view of the imaging element 27, the interference filter 43 is inserted into the optical path of the illumination light by the spectral control unit 45. Thus, only the light in the blue region that has passed through the interference filter 43 among the illumination light emitted from the xenon lamp 41 is emitted from the light source unit 13 and irradiated onto the observation region.

[0097] According to this modification, the spectral control unit 45 automatically switches the insertion and extraction of the interference filter 43 during normal observation and when a field-of-view defect occurs. Thus, illumination light of white light is irradiated during normal observation, and illumination light in the blue region is irradiated when a field-of-view defect occurs. As a result, it is possible to ensure the color tone of the endoscopic image in cases such as normal observation when there is no field-of-view defect caused by calculus fragments by a simple operation. In addition, it is possible to ensure the field of view without increasing the irrigation flow rate when a field-of-view defect caused by calculus fragments occurs.

[0098] [Second Embodiment]

[0099] Next, an endoscopic system according to a second embodiment of the present invention will be described.

[0100] As shown Figure 7 The endoscopic system 51 of the present embodiment is different from that of the first embodiment in that it includes an oscillation condition determination unit (determination unit) 53 that determines the oscillation conditions of the laser of the laser oscillator 7.

[0101] Hereinafter, parts having the same structure as those of the endoscopic system 1 of the first embodiment are denoted by the same reference numerals and description thereof is omitted.

[0102] The oscillation condition determination unit 53 determines whether poor field of view is caused by stone fragments according to the oscillation conditions of the laser emitted by the laser pulse generation device 3. Specifically, the oscillation condition determination unit 53 determines whether the oscillation conditions of the laser oscillator 7 satisfy the following conditional expressions (1) to (3).

[0103] Moreover, the oscillation condition determination unit 53 determines that poor field of view has occurred when the oscillation conditions of the laser oscillator 7 satisfy all of the conditional expressions (1) to (3), and determines that poor field of view has not occurred when any one of the conditional expressions (1) to (3) is not satisfied.

[0104] The wavelength of the laser emitted from the laser oscillator 7 is 1900 nm to 3000 nm (1)

[0105] The energy of the laser emitted from the laser oscillator 7 is 200 mJ to 400 mJ (2)

[0106] The frequency of the laser emitted from the laser oscillator 7 is 50 Hz to 80 Hz (3)

[0107] The oscillation condition determination unit 53 is implemented by the above-described processor and storage device. That is, an oscillation control program is stored in the storage device. And, by the processor, according to the oscillation control program, the above processing of the oscillation condition determination unit 53 is executed. The oscillation condition determination unit 53 may also include a processor and a storage unit. The determination result of the oscillation condition determination unit 53 is sent to the light source control unit 31.

[0108] When the light source control unit 31 is input with the determination result that poor field of view has not occurred from the oscillation condition determination unit 53, it emits white light illumination light from the light source unit 13 by driving each of the LEDs 33B, 33G, and 33R. In addition, when the light source control unit 31 is input with the determination result that poor field of view has occurred from the oscillation condition determination unit 53, it increases the emission light amount of the B-LED 33B, and on the other hand, decreases the emission light amounts of the G-LED 33G and the R-LED 33R, thereby switching the illumination light emitted from the light source unit 13 to light in the blue region.

[0109] If the oscillation conditions of the laser satisfy all of the conditional expressions (1) to (3), the calculus can be shattered into relatively small granular forms. When the calculus fragments are in relatively small granular forms, there is a high possibility that the endoscopic image looks turbid. On the other hand, when any one of the conditional expressions (1) to (3) is not satisfied by the oscillation conditions of the laser, it is difficult for the calculus fragments to become small granular forms, and the possibility that the endoscopic image looks turbid is low.

[0110] According to the endoscopic system 51 of the present embodiment, when the oscillation conditions of the laser oscillator 7 satisfy all of the conditional expressions (1) to (3), it is determined that a poor field of view due to calculus fragments has occurred, and the illumination light emitted from the light source unit 13 is automatically switched to the light in the blue region by the light source control unit 31. Thereby, when a poor field of view due to calculus fragments has not occurred, the tone of the endoscopic image can be ensured, and when a poor field of view due to calculus fragments occurs, the field of view can be ensured by a simple operation without increasing the irrigation flow rate.

[0111] This modification example can be modified into the following structure.

[0112] In the present embodiment, for example, as Figure 8 shown, the light source unit 13 may include a xenon lamp 41 and an interference filter 43, and may include a spectral control unit (control unit) 45 instead of the light source control unit 31. Further, the spectral control unit 45 may insert or remove the interference filter 43 with respect to the optical path of the illumination light emitted from the xenon lamp 41 according to the determination result of the oscillation condition determination unit 53, thereby switching the spectral distribution of the illumination light.

[0113] That is, it may be determined by the oscillation condition determination unit 53 that a poor field of view has occurred when the oscillation conditions of the laser oscillator 7 satisfy all of the conditional expressions (1) to (3), and the interference filter 43 is inserted into the optical path of the illumination light by the spectral control unit 45. On the other hand, it may be determined by the oscillation condition determination unit 53 that a poor field of view has not occurred when any one of the conditional expressions (1) to (3) is not satisfied, and the interference filter 43 is removed from the optical path of the illumination light by the spectral control unit 45.

[0114] Each of the above embodiments can be modified into the following structure.

[0115] For example, the light source unit 13 may include: an LED light source that generates illumination light of white light; and an optical filter (both are not shown), which is disposed in the optical path of the illumination light emitted from the LED light source in a manner that can be inserted or removed.

[0116] Further, the light source control unit 31 may also switch the spectral distribution of the illumination light by inserting and removing an optical filter into and from the optical path of the illumination light according to the determination result of the image processing unit 19 or the oscillation condition determination unit 53. As the optical filter, for example, a color filter that only transmits light in the blue region, a low-pass filter, a band-pass filter, or the like may be used.

[0117] As described above, the embodiments of the present invention have been described in detail with reference to the accompanying drawings. However, the specific structure is not limited to this embodiment, and also includes design changes and the like within the scope not departing from the gist of the present invention. For example, the present invention is not limited to being applied to the above-described respective embodiments and modification examples, and may also be applied to embodiments in which these embodiments and modification examples are appropriately combined, without particular limitation. In addition, in the above-described respective embodiments, the treatment of urinary tract stones has been illustrated as an example, but for example, it may also be applied to other treatments such as the treatment of bile duct stones.

[0118] Reference Numeral Explanation

[0119] 1, 51: Endoscope system;

[0120] 3: Laser pulse generation device;

[0121] 5: Endoscope device;

[0122] 13: Light source unit (light source);

[0123] 19: Image processing unit (determination unit, calculation unit);

[0124] 27: Imaging element (imaging unit);

[0125] 31: Light source control unit (control unit);

[0126] 43: Interference filter;

[0127] 45: Spectral control unit (control unit);

[0128] 53: Oscillation condition determination unit (determination unit).

Claims

1. An endoscope device, comprising: A light source capable of switching the spectral distribution of illumination light; An imaging unit that obtains an image by receiving the reflected light of the illumination light; A determination unit that determines whether a field-of-view defect caused by stone fragments has occurred within the field of view of the imaging unit, the stone fragments being fragments of a stone broken by irradiating a laser from a laser pulse generation device; And A control unit that controls the light source based on the determination result of the determination unit, When it is determined by the determination unit that the field-of-view defect has not occurred, the control unit emits the illumination light of white light from the light source, and when it is determined that the field-of-view defect has occurred, the control unit switches the illumination light emitted from the light source to light in the blue region.

2. The endoscope device according to claim 1, wherein The light in the blue region is light having a wavelength of 500 nm or less with the strongest intensity.

3. The endoscope device according to claim 1, wherein The determination unit determines whether the field-of-view defect has occurred based on a parameter related to the amount of high-frequency components higher than a specified frequency in the image.

4. The endoscope device according to claim 3, wherein The parameter is a spectral component.

5. The endoscope device according to claim 4, wherein The endoscope device has a calculation unit that calculates a ratio of the cumulative value of the spectral components higher than the specified frequency to the cumulative value of the spectral components lower than the specified frequency, When the ratio calculated by the calculation unit is greater than a specified threshold value, the determination unit determines that the field-of-view defect has occurred.

6. The endoscope device according to claim 1, wherein The determination unit determines whether the field-of-view defect has occurred based on the oscillation conditions of the laser emitted from the laser pulse generation device.

7. The endoscope device according to claim 6, wherein When the oscillation conditions satisfy all of the following conditional expressions (1) to (3), the determination unit determines that the field-of-view defect has occurred: The wavelength of the laser is 1900 nm to 3000 nm (1) The energy of the laser is 200 mJ to 400 mJ (2) The frequency of the laser is 50 Hz to 80 Hz (3).

8. The endoscope device according to claim 1, wherein The light source has a xenon lamp and an interference filter disposed in the optical path of the illumination light emitted from the xenon lamp in a pluggable manner, The control unit switches the spectral distribution of the illumination light by plugging and unplugging the interference filter with respect to the optical path of the illumination light.

9. The endoscope device according to claim 1, wherein The light source includes a plurality of LED light sources that emit light of different colors, The control unit switches the spectral distribution of the illumination light by changing the LED light sources to be driven.

10. The endoscope device according to claim 1, wherein The light source has an LED light source and an optical filter disposed in the optical path of the illumination light emitted from the LED light source in a pluggable manner, The control unit switches the spectral distribution of the illumination light by inserting and removing the optical filter with respect to the optical path of the illumination light.

11. An endoscope system, comprising: A laser pulse generating device that irradiates a stone with a laser; and An endoscope device, comprising: A light source capable of switching the spectral distribution of the illumination light; An imaging unit that acquires an image by receiving the reflected light of the illumination light; A determination unit that determines whether a field of view defect caused by stone fragments has occurred within the field of view of the imaging unit, the stone fragments being fragments of a stone broken by irradiating the stone with a laser from the laser pulse generating device; And A control unit that controls the light source based on the determination result of the determination unit, When it is determined by the determination unit that the field of view defect has not occurred, the control unit emits the illumination light of white light from the light source, and when it is determined that the field of view defect has occurred, the control unit switches the illumination light emitted from the light source to light in the blue region.

12. The endoscope system according to claim 11, wherein The light in the blue region is light having a wavelength of 500 nm or less with the strongest intensity.

13. The endoscope system according to claim 11, wherein The determination unit determines whether the field of view defect has occurred based on a parameter related to the amount of high-frequency components higher than a specified frequency in the image.

14. The endoscope system according to claim 13, wherein The parameter is a spectral component.

15. The endoscope system according to claim 14, wherein The endoscope system has a calculation unit that calculates the ratio of the cumulative value of the spectral components higher than the specified frequency to the cumulative value of the spectral components lower than the specified frequency, When the ratio calculated by the calculation unit is greater than a specified threshold, the determination unit determines that the field of view defect has occurred.

16. The endoscope system according to claim 11, wherein The determination unit determines whether the field of view defect has occurred based on the oscillation conditions of the laser emitted from the laser pulse generating device.

17. The endoscope system according to claim 16, wherein When the oscillation conditions satisfy all of the following conditional expressions (1) to (3), the determination unit determines that the field of view defect has occurred: The wavelength of the laser is 1900 nm to 3000 nm (1) The energy of the laser is 200 mJ to 400 mJ (2) The frequency of the laser is 50 Hz to 80 Hz (3).

18. The endoscope system according to claim 11, wherein The light source has a xenon lamp and an interference filter disposed in a pluggable manner in the optical path of the illumination light emitted from the xenon lamp, The control unit switches the spectral distribution of the illumination light by inserting and removing the interference filter with respect to the optical path of the illumination light.

19. The endoscope system according to claim 11, wherein The light source includes a plurality of LED light sources that emit light of different colors, The control unit switches the spectral distribution of the illumination light by changing the LED light source to be driven.

20. The endoscope system according to claim 11, wherein, the light source has an LED light source and an optical filter disposed in an optical path of the illumination light emitted from the LED light source in a pluggable manner, the control unit switches a spectral distribution of the illumination light by plugging and unplugging the optical filter with respect to the optical path of the illumination light.

Images