JP2010148646A - Endoscope, endoscope system and method of driving endoscope - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To completely prevent light from leakage by a simple construction in an endoscope using a laser light source. <P>SOLUTION: The connector 15 of an electronic endoscope 10 contains photoelectric conversion device 32, a laser light source driver 33 and a laser light source 34. Xenon light that is generated from a light source 12 and enters the photoelectric conversion device 32 after passing through a light guide 31 used for xenon light undergoes photoelectric conversion in the photoelectric conversion device 32, which outputs the electric charge and voltage corresponding to the light quantity of xenon light to the laser light source driver 33. The laser light source driver 33 determines the laser light quantity corresponding to the amplitude of input voltage, and drives the laser light source 34 so that laser light in the determined light quantity can be emitted. The emitted laser light is led to a phosphor 36 via a light guide 35 for laser light. The phosphor 36 is excited by laser light and discharges white illumination light. The white illumination light is dispersed by an illumination lens 24 and irradiated on an inner region for observation within the body cavity via an illumination window 21. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to an endoscope, an endoscope system, and an endoscope driving method for irradiating illumination light to an observation site in a subject in order to observe the subject.

  Conventionally, examination using an endoscope, for example, an electronic endoscope, has been widely used in the medical field. The electronic endoscope has a solid-state imaging device such as a CCD image sensor at the tip of an insertion portion to be inserted into a subject. The electronic endoscope is connected to the processor device and the light source device via a cord and a connector.

  The processor device performs various processes on the imaging signal output from the solid-state imaging device, and generates an endoscopic image for diagnosis. The endoscopic image is displayed on a monitor connected to the processor device. The light source device has a light source for supplying illumination light for in-subject illumination to the electronic endoscope. Illumination light from the light source is guided to the distal end of the insertion portion by a light guide inserted through the electronic endoscope.

  Conventionally, a white light source such as a xenon lamp or a halogen lamp has been used as a light source, but recently, a light source device using a laser light source has been proposed instead (see Patent Documents 1 to 3). Since the laser beam has a small beam diameter, the diameter of the light guide can be reduced compared to the case of using a conventional white light source. Thereby, the diameter of the insertion part of an electronic endoscope can be made thinner.

  Furthermore, in the field of medical diagnosis using electronic endoscopes, light in a narrow wavelength band is observed rather than observation with white light having broad spectral characteristics in the visible light range in order to facilitate the detection of lesions. Special light observation is also performed in which a region is irradiated and reflected light is imaged and observed. When a laser light source is used, special light observation can be performed with a relatively simple configuration by using a wavelength conversion element such as a narrow-band wavelength laser or an etalon.

  By the way, the light from the light source may leak light or the like that is irregularly reflected in the light source device from a socket of the light source device or other openings (such as ventilation openings) provided in the housing (hereinafter referred to as leakage light). When a laser light source is used, there is a risk of blindness if laser light having strong energy leaks from the casing and enters the eyes of the operator or the subject. Therefore, it is necessary to strictly prevent the occurrence of leakage light.

Therefore, as a countermeasure against leakage light, Patent Document 1 determines that there is an abnormality in the optical system when a photometric sensor is provided on the optical path of the laser beam in the light source device and the amount of light received by the photometric sensor is lower than a threshold value. Laser light emission is stopped. In Patent Document 2, a system control circuit and an electrical socket are provided in the light source device, a ROM in which identification information is stored in the connector of the endoscope, and the ROM in the connector is connected to the system control circuit via the electrical socket. Laser light is emitted only while identification information indicating that the endoscope is a laser light compatible endoscope is being read. In Patent Literature 3, the laser light is prevented from leaking from the optical system by covering the optical surface of the laser light source and the optical system such as the collimator lens with a laser light source case.
JP 2005-348792 A JP 2005-348793 A JP 2005-348794 A

  In Patent Documents 1 to 3, a measure for preventing laser light from being emitted from the socket when the endoscope is not connected to the socket of the light source device, and for preventing the laser light from leaking outside the optical system Although countermeasures have been proposed, in order to implement these countermeasures, it is necessary to add a large number of parts to the conventional apparatus, which makes the apparatus large.

  Further, since the laser beam has a small beam diameter, if the connection between the socket of the light source device and the connector of the endoscope is slightly shifted, the laser beam is not incident on the light guide. For this reason, high mounting accuracy is required not only for the optical system in the light source device but also for the connection portion between the socket and the connector. In addition, since the connector is frequently detached from the socket, a high mechanical strength that does not cause backlash is required even if the number of removals is repeated. As described above, when the laser light source is built in the light source device, it is extremely difficult to completely prevent leakage light and transmit all the laser light to the endoscope side, and even if possible, the cost is high.

  The present invention has been made in view of the above problems, and an object of the present invention is to completely prevent light leakage with a simple configuration while using a laser light source.

  In order to achieve the above object, an endoscope of the present invention is characterized by including a laser light source that irradiates illumination light to an observation site in a subject.

  It is preferable to further include a control unit that controls driving of the laser light source. Moreover, it is preferable to further include a photoelectric conversion element that photoelectrically converts light emitted from the light source of the light source device based on luminance information of the endoscopic image. In this case, the control unit determines the amount of laser light emitted from the laser light source according to the output of electrical energy generated by the photoelectric conversion element. The light source of the light source device is, for example, a xenon light source or a halogen light source mounted on a conventional light source device.

  The photoelectric conversion element is a photodiode, for example, and may be a solar cell. In the case of a solar cell, electric energy generated in the solar cell is used as driving energy for the laser light source.

  The control unit may determine the amount of laser light emitted from the laser light source based on luminance information of an endoscopic image directly input from the processor device.

  In addition, the endoscope of the present invention includes a laser light source that irradiates an observation site in a subject with illumination light, a control unit that controls driving of the laser light source, and a light source based on luminance information of an endoscope image. A photoelectric conversion element that photoelectrically converts light emitted from the light source of the device, and the control unit determines the amount of laser light emitted from the laser light source according to the output of electrical energy generated by the photoelectric conversion element It is characterized by doing.

  An endoscope system according to the present invention includes an endoscope having a laser light source that irradiates an observation site in a subject with illumination light, and a processor device that outputs luminance information of an endoscopic image. Is controlled based on the luminance information.

  The endoscope preferably further includes a control unit that controls driving of the laser light source and a photoelectric conversion element that photoelectrically converts light emitted from the light source of the light source device based on the luminance information. In this case, the control unit determines the amount of laser light emitted from the laser light source according to the output of electrical energy generated by the photoelectric conversion element.

  Or the said control part determines the light quantity of the laser beam irradiated from the said laser light source based on the said brightness | luminance information input directly from the said processor apparatus.

  The endoscope driving method according to the present invention includes a first step of obtaining luminance information of an endoscopic image by a processor device, and a laser light source built in the endoscope based on the luminance information obtained in the first step. And a second step for controlling the driving of the motor.

  In the second step, light emitted from the light source of the light source device is photoelectrically converted by a photoelectric conversion element built in the endoscope based on the luminance information. And the light quantity of the laser beam irradiated from a laser light source is determined according to the output of the electrical energy which generate | occur | produced with the photoelectric conversion element.

  Alternatively, in the first step, the luminance information is obtained directly from the processor device. In the second step, the amount of laser light emitted from the laser light source is determined based on the directly acquired luminance information.

  According to the present invention, since the laser light source is provided in the endoscope, it is possible to completely prevent the problem of leakage light that occurs when the laser light source is built in the light source device. In addition, if the driving of the laser light source of the endoscope is controlled based on the amount of electrical energy obtained by photoelectrically converting the light from the light source device, only the endoscope can be changed from the conventional endoscope system based on the use of the white light source. It is possible to inspect a subject using a laser light source only by exchanging for the one of the present invention. Furthermore, if the luminance information of the endoscopic image generated by the processor device is sent directly to the endoscope, the endoscope system is configured by only the endoscope of the present invention and the conventional processor device, that is, the light source device It can be omitted.

  In FIG. 1, the endoscope system 2 includes an electronic endoscope 10, a processor device 11, and a light source device 12. As is well known, the electronic endoscope 10 includes a flexible insertion portion 13 that is inserted into a body cavity of a patient, an operation portion 14 that is connected to a proximal end portion of the insertion portion 13, a processor device 11, and a light source. A connector 15 connected to the apparatus 12, an operation unit 14, and a universal cord 16 that connects the connectors 15 are included.

  An observation window 20, an illumination window 21 (both see FIG. 2) and the like are provided at the distal end of the insertion portion 13. In the back of the observation window 20, a solid-state image sensor 23 for intra-body cavity imaging is disposed via an objective optical system 22 (see FIG. 2 for both). The illumination window 21 irradiates an observation site with illumination light guided by a laser light source 34, a laser light guide 35, a phosphor 36, and an illumination lens 24 (see FIG. 2).

  The operation unit 14 includes an angle knob for bending the distal end of the insertion unit 13 in the vertical and horizontal directions, an air supply / water supply button for ejecting air and water from the distal end of the insertion unit 13, and an endoscopic image. A freeze button or the like for recording a still image is provided.

  Further, a forceps port through which a treatment tool such as an electric knife is inserted is provided on the distal end side of the operation unit 14. The forceps opening communicates with a forceps outlet provided at the distal end of the insertion portion 13 through a forceps channel in the insertion portion 13.

  The processor device 11 is electrically connected to the light source device 12 and comprehensively controls the operation of the endoscope system 2. The processor device 11 supplies power to the electronic endoscope 10 via the universal cord 16 or a transmission cable inserted into the insertion portion 13 and controls the driving of the solid-state imaging device 23. In addition, the processor device 11 receives the imaging signal output from the solid-state imaging device 23 via the transmission cable, and performs various processes on the received imaging signal to generate image data. The image data generated by the processor device 11 is displayed as an endoscopic image on a monitor 17 connected to the processor device 11 by a cable.

  In FIG. 2, the electronic endoscope 10 includes the observation window 20, the illumination window 21, the objective optical system 22, the solid-state imaging device 23, and the illumination lens 24 provided at the distal end of the insertion unit 13, and an analog signal processing circuit ( (Hereinafter abbreviated as AFE) 25 and the like are provided in the operation unit 14.

  The solid-state image sensor 23 is composed of an interline transfer type CCD image sensor, a CMOS image sensor, or the like. The solid-state imaging device 23 is arranged so that image light of an observation site in the body cavity that passes through the observation window 20 and the objective optical system 22 (consisting of a lens group and a prism) is incident on the imaging surface. On the imaging surface of the solid-state imaging device 23, a color filter composed of a plurality of color segments (for example, a primary color filter with a Bayer array, not shown) is formed.

  The AFE 25 includes a correlated double sampling circuit (hereinafter abbreviated as CDS) 26, an automatic gain control circuit (hereinafter abbreviated as AGC) 27, and an analog / digital converter (hereinafter abbreviated as A / D) 28. Yes. The CDS 26 performs correlated double sampling processing on the image signal output from the solid-state image sensor 23, and removes reset noise and amplifier noise generated in the solid-state image sensor 23. The AGC 27 amplifies the imaging signal from which noise has been removed by the CDS 26 with a gain (amplification factor) specified by the processor device 11. The A / D 28 converts the imaging signal amplified by the AGC 27 into a digital signal having a predetermined number of bits. The imaging signal digitized by the A / D 28 is input to the processor device 11 via the universal code 16 and the connector 15 and is stored in a working memory (not shown) of a digital signal processing circuit (hereinafter abbreviated as DSP) 43. Once stored.

  In addition to the AFE 25, the operation unit 14 of the electronic endoscope 10 is provided with a CPU 29 and a timing / driver circuit 30. The CPU 29 communicates with the CPU 40 of the processor device 11 and controls the operation of each unit such as the AFE 25 and the timing / driver circuit 30.

  The timing / driver circuit 30 doubles as a timing generator and a driver for the solid-state imaging device 23. The timing / driver circuit 30 generates various drive pulses for driving the solid-state imaging device 23 and a synchronization pulse for the AFE 25. The solid-state imaging device 23 performs an imaging operation according to the drive pulse from the timing / driver circuit 30 and outputs an imaging signal. Each unit 26 to 28 of the AFE 25 operates based on a synchronization pulse from the timing / driver circuit 30.

  After the electronic endoscope 10 and the processor device 11 are connected, the CPU 29 drives the timing / driver circuit 30 and adjusts the gain of the AGC 27 in accordance with an operation start instruction from the CPU 40 of the processor device 11.

  The CPU 40 controls the overall operation of the processor device 11. The CPU 40 is connected to each unit via a data bus, an address bus, and a control line (not shown). The ROM 41 stores various programs (OS, application programs, etc.) and data (graphic data, etc.) for controlling the operation of the processor device 11. The CPU 40 reads out necessary programs and data from the ROM 41, develops them in the RAM 42 which is a working memory, and sequentially processes the read programs. Further, the CPU 40 obtains information that changes for each examination, such as examination date and time, character information such as patient and surgeon information, from the operation unit 46 and a network such as a LAN (Local Area Network) and stores the information in the RAM 42.

  The DSP 43 reads the image signal from the AFE 25 from the work memory. The DSP 43 performs various signal processing such as color separation, color interpolation, gain correction, white balance adjustment, and gamma correction on the read image pickup signal to generate image data. The image data generated by the DSP 43 is input to a working memory (not shown) of a digital image processing circuit (hereinafter abbreviated as DIP) 44.

  The DIP 44 executes various image processing according to the control of the CPU 40. The DIP 44 reads the image data processed by the DSP 43 from the work memory. The DIP 44 performs various types of image processing such as electronic scaling, color enhancement, edge enhancement, spectral characteristic extraction, and the like on the read image data. The image data that has been subjected to various image processing by the DIP 44 is input to the display control circuit 45.

  The display control circuit 45 has a VRAM that stores processed image data from the DIP 44. The display control circuit 45 receives graphic data in the ROM 41 and RAM 42 from the CPU 40. The graphic data includes a display mask that hides the invalid pixel area of the endoscopic image and displays only the effective pixel area, character information such as examination date and time, patient and surgeon information, a graphical user interface (GUI). Interface). The display control circuit 45 performs various display control processes such as a display mask, character information, GUI superimposition processing, and drawing processing on the display screen of the monitor 17 on the image data from the DIP 44.

  The display control circuit 45 reads the image data from the VRAM and converts the read image data into a video signal (component signal, composite signal, etc.) corresponding to the display format of the monitor 17. Thereby, an endoscopic image is displayed on the monitor 17.

  The operation unit 46 is an operation panel provided on the housing of the processor device 11 or a known input device such as a mouse or a keyboard. The CPU 40 operates each unit in response to an operation signal from the operation unit 46.

  The power supply circuit 47 is a so-called constant voltage source, and supplies various power supply voltages to the solid-state imaging device 23, the CPU 29, the timing / driver circuit 30, the laser light source 34, and the like of the electronic endoscope 10. In response to an instruction from the CPU 40, the power supply circuit 47 starts supplying power supply voltage.

  The photometry circuit 48 acquires an imaging signal for one frame input from the AFE 25, integrates the luminance values for all the pixels in the effective pixel region, and averages the integrated values over the total number of pixels, thereby obtaining an endoscope. An average luminance value (photometric value) of the image is calculated. This average luminance value is input to the light source device 12 via the CPU 40. In the light source device 12, the amount of illumination light is adjusted so that the average luminance value becomes a predetermined value, that is, the brightness of the endoscopic image is constant.

  In addition to the above, the processor device 11 includes a compression processing circuit that performs image compression on image data in a predetermined compression format (for example, JPEG format), and the compressed image data as a CF card or magneto-optical disk (MO). In addition, a media I / F stored in a removable medium such as a CD-R, a network I / F that performs transmission control of various data with a network such as a LAN, and the like are provided. These are connected to the CPU 40 via a data bus or the like.

  The light source device 12 includes a xenon light source 50. The xenon light source 50 is driven by a xenon light source driver 51. The aperture mechanism 52 is disposed on the light emission side of the xenon light source 50 and adjusts the amount of xenon light emitted from the xenon light source 50 so that the brightness of the endoscopic image displayed on the monitor 17 is substantially constant. . The aperture mechanism 52 includes an aperture blade that changes the aperture diameter that allows xenon light to pass through, and a motor that moves the aperture blade. The aperture mechanism 52 changes the passage area of the xenon light to change the aperture of the condensing lens 53. Increase or decrease the amount of incident xenon light.

  The CPU 54 communicates with the CPU 40 of the processor device 11, and drives the aperture mechanism 52 to change the aperture diameter according to the average luminance value of the image data calculated by the photometry circuit 48 of the processor device 11. Specifically, when increasing the amount of xenon light, the aperture blades of the aperture mechanism 52 are opened to increase the light diameter of the xenon light. On the other hand, when reducing the amount of xenon light, the aperture blade of the aperture mechanism 52 is closed to reduce the light diameter of the xenon light. A series of these controls is the same as that generally performed in a light source device having a xenon light source.

  The condensing lens 53 condenses the xenon light that has passed through the aperture mechanism 52 and guides it to the incident end of the light guide 31 for xenon light. For example, the xenon light guide 31 is formed by bundling a plurality of quartz optical fibers with a wound tape or the like. The light guide 31 for xenon light has an incident end arranged on the connector 15 of the electronic endoscope 10, and the xenon light is condensed by the condenser lens 53 when the connector 15 is inserted into the light source device 12. The incident end is arranged at the position.

  In the connector 15 of the electronic endoscope 10, a photoelectric conversion element 32, a laser light source driver 33, and a laser light source 34 are housed. The exit end of the light guide 31 for xenon light is arranged immediately before the photoelectric conversion element 32, and the xenon light guided to the exit end of the light guide 31 for xenon light enters the photoelectric conversion element 32. The photoelectric conversion element 32 is a device that converts light energy into electrical energy, for example, a photodiode, etc., photoelectrically converts incident xenon light, generates charges according to the amount of light, and converts the charge voltage into a laser light source driver. To 33. The laser light source driver 33 controls driving of the laser light source 34 by changing a signal (for example, a pulsed timing signal) supplied to the laser light source 34 based on the input voltage from the photoelectric conversion element 32.

  The laser light source driver 33 performs photoelectric conversion using a conversion formula for converting input from the photoelectric conversion element 32 into laser light output, a data table storing correspondence between the input from the photoelectric conversion element 32 and laser light output, or the like. The laser light output corresponding to the input from the element 32 is derived, and the laser light source 34 is driven so as to obtain the derived laser light output. Accordingly, the amount of laser light emitted from the laser light source 34 is also increased or decreased following the increase or decrease of the amount of xenon incident on the photoelectric conversion element 32.

  The laser light emitted from the laser light source 34 enters the laser light guide 35. The laser light guide 35 is, for example, a bundle of a plurality of quartz optical fibers converged by a winding tape or the like, like the xenon light guide 31, but the laser light guide 35 is more suitable. It has a smaller diameter than the light guide 31 for xenon light.

  A phosphor 36 that is excited by the laser light and emits white light is attached to the emission end of the laser light guide 35. The white illumination light emitted from the phosphor 36 is diffused by the illumination lens 24, and is irradiated to the site to be observed in the body cavity via the illumination window 21.

  Next, the operation of the endoscope system 2 configured as described above will be described with reference to FIG. When observing the inside of a patient's body cavity with the electronic endoscope 10, the surgeon connects the connector 15 of the electronic endoscope 10 to each device 11, 12 and turns on the power of each device 11, 12. Then, the operation unit 46 is operated to instruct the start of examination (S10), and the insertion unit 13 is inserted into the body cavity.

  Xenon light is emitted from the xenon light source 50 inside the light source device 12 (S11). The xenon light undergoes light amount adjustment by the diaphragm mechanism 52 (for example, the initial value is the minimum diaphragm) (S12), and then the xenon light guide 31. And enters the photoelectric conversion element 32 accommodated in the connector 15 of the electronic endoscope 10. The photoelectric conversion element 32 performs photoelectric conversion (S13) on the incident xenon light, generates a charge corresponding to the amount of light, and outputs this charge voltage to the laser light source driver 33.

  The laser light source driver 33 determines the amount of laser light based on the input from the photoelectric conversion element 32 (S14), and drives the laser light source 34 so as to emit the determined amount of laser light (S15). The laser light emitted from the laser light source 34 is guided to the phosphor 36 through the laser light guide 35. The phosphor 36 is excited by laser light to emit white illumination light.

  The white illumination light is diffused by the illumination lens 24 and is irradiated to the site to be observed in the body cavity via the illumination window 21. While illuminating the body cavity with the white illumination light, an endoscope image is captured by the solid-state imaging device 23 of the electronic endoscope 10 (S16), and the endoscope image is observed on the monitor 17 through image processing in the processor device 11. To do.

  At this time, the photometric value of the endoscopic image is obtained by the photometric circuit 48 of the processor unit 11 (S17). The CPU 54 of the light source device 12 communicates with the CPU 40 of the processor device 11 to evaluate the photometric value, and performs the xenon light amount adjustment (S12) by the diaphragm mechanism 52. When the photometric value is lower than the predetermined value, the CPU 54 increases the xenon light quantity by driving the aperture mechanism 52 to increase the light diameter of the xenon light. When the photometric value is higher than a predetermined value, the xenon light amount is reduced by reducing the light diameter of the xenon light.

  An increase in the amount of xenon light emitted from the light source device 12 (taken into the electronic endoscope 10 from the light source device 12) means an increase in the amount of photoelectric conversion (S13), that is, from the photoelectric conversion element 32 to the laser light source driver. This means that the input voltage to 33 increases. Based on the increased output, the laser light source driver 33 determines to increase the amount of laser light (S14), and drives the laser light source 34 to emit the increased amount of laser light (S15). Therefore, when the amount of xenon light emitted from the light source device 12 increases, the amount of laser light emitted from the laser light source 34 in the electronic endoscope 10 increases accordingly. Conversely, when the xenon light quantity decreases, the laser light quantity also decreases.

  The endoscope system 2 repeats the above-described processes of S12 to S17 until the surgeon operates the operation unit 46 and instructs the end of the examination (yes in S18).

  As described above, since the laser light source 34 is accommodated in the electronic endoscope 10, leakage light is completely prevented without requiring any special measures, and the laser beam is irradiated safely and highly efficiently on the site to be observed. be able to. Also, the light amount control of the laser light source 34 can be performed by using the processor device 11 and the light source device 12 having the same configuration as the conventional one by providing the photoelectric conversion element 32. Only the endoscope needs to be changed to that of the present invention, and compatibility with conventional devices is also ensured. Since only xenon light is handled in the light source device 12 as in the past, the risk due to leakage light is less than the laser light and the beam diameter is larger, so compared to the conventional one in which the laser light source is mounted on the light source device, There is no need for special considerations regarding the mounting accuracy and mechanical strength of connectors and sockets.

  In the above embodiment, the photoelectric conversion element 32 is used only as a measurement unit that measures the amount of xenon light from the light source device 12, and the laser light source 34 is driven by the power supplied from the power supply circuit 47 in the processor device 11. However, the electrical energy generated by the photoelectric conversion element may be used for driving the laser light source 34.

  In this case, a solar cell 61 is used as a photoelectric conversion element as in an electronic endoscope 60 shown in FIG. 4 (the same components as those in the above embodiment are denoted by the same reference numerals and description thereof is omitted). When xenon light enters the solar cell 61 from the light guide 31 for xenon light, the solar cell 61 generates electric power according to the amount of incident xenon light. For example, a part of this electric power is sent to the laser light source driver 33 and used to determine the amount of laser light, while the rest is sent to the laser light source 34 and used as an auxiliary power source for the laser light source 34. The power sent to the laser light source driver 33 and the power sent to the laser light source 34 are set to a constant ratio, for example.

  When the power generated by the solar cell 61 is sufficient to drive the laser light source 34, the power supply from the power supply circuit 47 is not necessary. Furthermore, if the power generated by the solar cell 61 has a margin, the power can be supplied to the solid-state imaging device 23, the CPU 29, the timing / driver circuit 30, and the like. Alternatively, in addition to or instead of the power supply circuit 47, a battery may be stacked on the electronic endoscope 60 and the battery may be charged with electric power generated by the solar cell 61. As described above, by using the solar cell, the energy of the xenon light from the light source device can be effectively used, so that the power consumption efficiency of the electronic endoscope and thus the entire endoscope system can be increased.

  In the above embodiment, the light amount of the xenon light emitted from the light source device is measured on the electronic endoscope side using the light source device to determine the laser light amount from the laser light source, but the present invention is not limited to this. Absent. In the above embodiment, the photometric value of the image data calculated by the photometric circuit of the processor device and the control signal for the light source device, which are transmitted from the processor device to the light source device, are not sent from the CPU of the processor device to the CPU of the light source device. If it is sent directly to the CPU of the electronic endoscope, the light source device can be omitted from the endoscope system. For example, if a connector corresponding to an input terminal from a processor device provided in a conventional light source device is provided in an electronic endoscope, the above configuration can be implemented without changing the control of the processor device.

  In this case, like the electronic endoscope 65 shown in FIG. 5 (the same components as those in the above-described embodiment are denoted by the same reference numerals and the description is omitted), the CPU communicates with the CPU of the processor device in the same manner as the CPU of the light source device. A CPU 66 is provided for directly obtaining the photometric value of the image data and evaluating the photometric value. When the photometric value is higher than the predetermined value, the CPU 66 instructs the laser light source driver 33 to reduce the laser light quantity. On the other hand, when the value is low, the CPU 66 instructs the laser light source driver 33 to increase the laser light quantity.

  In this manner, the photometric value of the image data is directly taken into the electronic endoscope from the processor device, and the driving of the laser light source is controlled based on the photometric value, thereby omitting the light source device from the conventional endoscope system. It is possible to simplify the system. In addition, a conventional processor device can be used as it is.

  In the above embodiment, the laser light is converted into white illumination light by the phosphor and then observed by irradiating the observation site in the body cavity. However, a narrow band wavelength laser is used as the laser light source, or laser Special light observation may be performed by providing a wavelength conversion element such as an etalon on the light emission side.

  In the above embodiment, the laser light source is housed in the connector of the electronic endoscope. However, the present invention is not limited to this. For example, the laser light source may be provided in the operation unit of the electronic endoscope. Furthermore, if there is a space, it may be arranged at the tip of the insertion part of the electronic endoscope. The more the laser light source is placed on the tip side of the electronic endoscope, the shorter the laser light path can be shortened, so even if the electronic endoscope breaks in the middle of the insertion section, there is a risk that the laser light will leak. It can be made smaller. Since the laser light source generates a large amount of heat, it is preferable to provide a member or mechanism that effectively radiates the heat.

  In the above embodiment, all the xenon light generated by the xenon light source of the light source device is incident on the photoelectric conversion element, and only the illumination light from the laser light source is irradiated from the electronic endoscope to the site to be observed. Part of the xenon light may be incident on the photoelectric conversion element, and the rest may be irradiated as illumination light from the electronic endoscope to the site to be observed.

  Furthermore, a mechanism for selectively irradiating one or both of laser light and xenon light to the site to be observed may be provided. In this way, when the laser light source is used for special light observation, normal light observation using xenon light and special light observation using laser light can be performed with one electronic endoscope. The trouble of exchanging the endoscope between light observation and special light observation can be saved.

  The light source built in the electronic endoscope is not limited to a laser, but may be an LED, for example. The light source mounted in the light source device is not limited to a xenon light source, and a white high-intensity light source such as a halogen light source may be used instead. Furthermore, the light source of the light source device is not limited to a gas lamp, and a known light source such as an LED may be used. Further, if the xenon light from the light source device is directly incident on the photoelectric conversion element, the light guide for xenon light is not necessary.

  In the above embodiment, adjustment of the amount of laser light from the laser light source is performed by a change in the signal supplied from the laser light source driver to the laser light source, but if there is a space in the electronic endoscope, the xenon light source of the light source device is used. Similarly to the adjustment of the xenon light quantity, a diaphragm mechanism for laser light may be provided.

  In the above embodiment, an electronic endoscope is exemplified as an endoscope, but an ultrasonic endoscope may be used. Further, the processor device and the light source device may be separate as in the above embodiment, or may be integrated. Further, the present invention may be applied to other endoscopes such as an endoscope that observes an affected part through a fiberscope. Furthermore, in the above embodiment, a medical endoscope having a patient as a subject has been exemplified, but an industrial endoscope having a pipe or the like as a subject may be used.

It is an external view which shows the structure of an endoscope system. It is a block diagram which shows the structure of an endoscope system. It is a flowchart which shows the process sequence of an endoscope system. It is a block diagram which shows the structure of the endoscope system in another embodiment of this invention. It is a block diagram which shows the structure of the endoscope system in another embodiment of this invention.

Explanation of symbols

2 Endoscope system 10, 60, 65 Electronic endoscope 11 Processor unit 12 Light source unit 29, 66 CPU
31 Light guide for xenon light 32 Photoelectric conversion element 33 Laser light source driver 34 Laser light source 35 Light guide for laser light 40 CPU
48 Photometric circuit 50 Xenon light source 52 Aperture mechanism 54 CPU
61 Solar cell

Claims (12)

  An endoscope comprising a laser light source for irradiating illumination light to a site to be observed in a subject.   The endoscope according to claim 1, further comprising a control unit that controls driving of the laser light source. A photoelectric conversion element that photoelectrically converts light emitted from the light source of the light source device based on luminance information of the endoscopic image;
The endoscope according to claim 2, wherein the control unit determines the amount of laser light emitted from the laser light source in accordance with an output of electrical energy generated by the photoelectric conversion element. The photoelectric conversion element is a solar cell,
The endoscope according to claim 3, wherein electric energy generated in the solar cell is used as driving energy of the laser light source.   The endoscope according to claim 2, wherein the controller determines the amount of laser light emitted from the laser light source based on luminance information of an endoscopic image directly input from a processor device. mirror. A laser light source for irradiating illumination light to an observation site in the subject;
A control unit for controlling driving of the laser light source;
A photoelectric conversion element that photoelectrically converts light emitted from the light source of the light source device based on luminance information of the endoscopic image;
The said control part determines the light quantity of the laser beam irradiated from the said laser light source according to the output of the electrical energy which generate | occur | produced in the said photoelectric conversion element, The endoscope characterized by the above-mentioned. An endoscope having a laser light source for irradiating illumination light to an observation site in a subject;
A processor device that outputs luminance information of an endoscopic image,
The laser system is driven and controlled based on the luminance information. The endoscope includes a control unit that controls driving of the laser light source;
A photoelectric conversion element that photoelectrically converts light emitted from the light source of the light source device based on the luminance information;
The endoscope system according to claim 7, wherein the control unit determines the amount of laser light emitted from the laser light source according to an output of electrical energy generated by the photoelectric conversion element. The endoscope further includes a control unit that controls driving of the laser light source,
The endoscope system according to claim 7, wherein the control unit determines a light amount of laser light emitted from the laser light source based on the luminance information directly input from the processor device. A first step of obtaining brightness information of an endoscopic image in a processor device;
An endoscope driving method comprising: a second step of controlling driving of a laser light source built in the endoscope based on the luminance information obtained in the first step. In the second step, the light emitted from the light source of the light source device based on the luminance information is photoelectrically converted by a photoelectric conversion element built in the endoscope,
The endoscope driving method according to claim 10, wherein the amount of laser light emitted from the laser light source is determined in accordance with an output of electric energy generated by the photoelectric conversion element. In the first step, the luminance information is obtained directly from the processor device;
The endoscope driving method according to claim 10, wherein in the second step, the light amount of the laser light emitted from the laser light source is determined based on the directly acquired luminance information.

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