JP5412052B2 - Endoscope light source device - Google Patents

Description

  The present invention relates to an endoscope light source device capable of supplying blinking light.

  In general, an electronic endoscope system for diagnosing or treating the inside of a body cavity of a patient processes an image signal generated by the electronic scope that captures an image of the inside of the body cavity with an imaging device provided at a distal end portion. A video processor for outputting to a monitor and a light source device for supplying light for illuminating an observation site in the body cavity to an electronic scope. Some video processors incorporate a light source device. In such an electronic endoscope system, illumination light from a light source device is irradiated from the tip of an electronic scope into a body cavity, and reflected light reflected by the inner wall of the body cavity is photoelectrically converted by an imaging device such as a CCD. The electric charge generated by the photoelectric conversion is read as an image signal, transferred to a video processor, and output to a monitor.

Conventionally, in the above electronic endoscope system, an optical chopper (hereinafter referred to as “chopper”) synchronized with a field rate of an image sensor is used to clearly capture a moving subject. There is known a technique for shortening the exposure time. Patent Document 1 describes a light source device for an electronic endoscope that includes a chopper for blinking illumination light between a light guide and a light source in order to adjust the exposure time. The chopper described in Patent Literature 1 has a rotating disk having an opening and a light shielding part, and the rotating disk is arranged so as to cross the optical path of illumination light. When the turntable rotates at a constant rotation speed, the state in which the illumination light passes through the opening and the state in which the light is blocked by the light shielding unit are alternately repeated. For this reason, the light passing through the rotating disk becomes blinking light by the rotation of the rotating disk. The chopper is controlled to rotate in synchronization with the image signal transferred from the electronic scope. Thus, the exposure time in each field is adjusted to a fixed time.
Japanese Patent Publication No. 6-38134

  By the way, in recent years, an increase in the number of pixels of an image sensor used in an electronic endoscope system, more specifically, an increase in megapixels has been progressing. In an image sensor with a large number of pixels, it takes a long time to store charges during imaging, and accordingly, a transfer rate for transferring an image signal to a video processor is lowered. For example, the transfer rate of an image signal in an image sensor with 1.2 million pixels suitable for use in an electronic endoscope is about 30 Hz. When imaging with blinking light is performed using an electronic scope equipped with such an image sensor having a high pixel count, the chopper provided in the light source device has a frequency of about 30 Hz in synchronization with an image signal transferred from the electronic scope. Rotates at a frequency and blinks the illumination light.

  Usually, the blinking light by the chopper as described above is irradiated toward the inner wall of the body cavity while the electronic scope is inserted into the body cavity, so that it is not expected to enter the eyes of the operator or the patient. However, in practice, an electronic scope that emits blinking light before and after the examination may be placed in the examination room, and the blinking light may enter the eyes of an operator or other person in the examination room. In addition, when the illumination light of the electronic scope is used as illumination when observing a lesion removed from the body cavity and the oral cavity before the inspection, or when connecting with a fiberscope to the light source device for inspection For example, when the illumination light from the light source device is used for direct observation, blinking light enters the eyes of the operator or the like.

  Generally, the frequency of light that humans recognize as continuous light is 50 Hz or more. Therefore, the light that blinks at a frequency of 30 Hz as described above is also perceived as blinking light by the human eye. Therefore, in the situation where the flickering light is emitted outside the body cavity as described above, the flickering light is detected by the surgeon and the surrounding human beings, and the operator feels uncomfortable due to the flickering of the light, and the surgeon performs appropriate direct observation. The problem that it is not possible to do.

  Therefore, the present invention has been made in view of the above circumstances, and in a situation where blinking light enters the eyes of an operator or the like, it is possible to switch the frequency at which the illumination light blinks to a frequency range in which flicker does not feel. An object of the present invention is to provide an endoscope light source device.

In order to solve the above problems, according to the present invention, an endoscope light source device for supplying illumination light to an endoscope is disposed between and passes through a light source and a light guide of the endoscope. Synchronized from the endoscope, the illumination light blinking means for periodically blinking the illumination light, the control means for controlling the illumination light blinking means to blink the illumination light at the first frequency based on the signal from the endoscope Connection detection means for detecting whether or not an electronic endoscope is connected based on whether or not a signal is received is provided. In this endoscope light source device, the illumination light blinks so that the control means blinks the illumination light at a second frequency different from the first frequency when the connection detection means does not detect the connection of the electronic endoscope. It is characterized by controlling the means.

In this case, the second frequency is set to a higher value than the first frequency. The second frequency is preferably 50 Hz or more. With such a configuration, for example, when a fiberscope is connected to an endoscope light source device, illumination light that blinks at the second frequency is supplied to the fiberscope. Observation can be performed comfortably without feeling uncomfortable. In addition, since the connection detection means detects whether or not the electronic endoscope is connected based on whether or not the synchronization signal is received from the electronic endoscope, a simple determination process of the presence or absence of the signal Can determine whether to blink at the second frequency.

  Further, the second frequency is preferably an integer multiple of the first frequency. Thereby, even when the illumination light is blinked at the second frequency, the exposure time per frame is constant. For this reason, even if an electronic endoscope observation is performed using illumination light blinked at the second frequency, an image without flicker can be obtained.

  Further, the connection detecting means may have a limit switch, and may be configured to detect whether or not the electronic endoscope is connected based on a signal from the limit switch. With this configuration, it is determined whether or not the electronic endoscope is connected to the light source device via an electrical connection portion having a limit switch. Thus, for example, when a fiberscope or the like is connected without an electrical connection, it is determined that the second frequency should be blinked, and the operator can comfortably feel no discomfort due to flickering of the observation image. Observations can be made.

  The endoscope light source device may further include a manual operation unit that receives an operation by the user. In this case, it is preferable that the control means controls the illumination light blinking means so as to blink the illumination light at the second frequency when the manual operation unit accepts an operation by the user. With such a configuration, the illumination light can be surely blinked at the second frequency when a user (operator or the like) needs it.

  The endoscope light source device may further include an image change detection unit that detects a change in an image captured by the electronic endoscope. In this case, it is preferable that the control unit controls the illumination light blinking unit so as to blink the illumination light at the second frequency when the change of the captured image is not detected by the image change detection unit. According to such a configuration, when the electronic endoscope is placed in an examination room or the like (outside the body cavity) in a state where illumination light is emitted before and after endoscopic observation, unpleasant flickering light is emitted from the examination room. It is not released continuously. In this case, the image change detection unit may detect a change in the captured image based on a luminance signal or a color difference signal transmitted from the electronic endoscope.

  Therefore, according to the present invention, it is possible to provide an endoscope light source device capable of switching the frequency at which the illumination light flickers to a frequency range in which the flickering light does not feel an unpleasant flicker when the blinking light enters the eyes of an operator or the like. can do.

  Hereinafter, an endoscope light source device according to the present invention will be described with reference to the drawings.

  FIG. 1 is a block diagram showing a configuration of an electronic endoscope system 100 of the present embodiment. The electronic endoscope system 100 is a system for an operator to observe and diagnose the inside of a patient's body cavity. The electronic endoscope system 100 includes a processor 100A including the endoscope light source device of the present invention, an electronic scope 100B for imaging the body cavity, and a monitor 100C.

  The processor 100A includes a system controller 1, a timing controller 2, a light source unit 3, and an image processing unit 4. The system controller 1 and the timing controller 2 are circuit units for driving and synchronizing not only the main body of the processor 100A but also the entire electronic endoscope system 100. The light source unit 3 generates illumination light for illuminating the inside of the body cavity during imaging by the electronic scope 100B. The illumination light generated by the light source unit 3 is supplied to the light guide 5 of the electronic scope 100 </ b> B inserted into the light guide connection unit 102. The image processing unit 4 receives a signal (image signal) relating to an image in the body cavity imaged by the electronic scope 100B from the electronic scope 100B via the electrical connection unit 101, performs a predetermined process, and outputs the signal to the monitor 100C. . The processor 100A further receives the scope detection unit 12 that detects whether or not the electronic scope 100B is connected to the processor 100A, the frequency switching button 13 for switching the rotational frequency of the rotating plate 36 described later, and the electronic scope 100B. An image change detection unit 14 for detecting a change in the captured image is provided.

  The electronic scope 100B is detachably connected to the processor 100A via the electrical connection unit 101 and the light guide connection unit 102. The electronic scope 100B has a flexible insertion portion flexible tube that is inserted into the body cavity. A light guide 5 made of an optical fiber bundle as a light transmission path extends inside the electronic scope 100B. A light distribution lens 6 for irradiating the transmitted light to the outside (that is, inside the body cavity) is provided on the distal end side of the insertion tube of the light guide 5. In addition to the light distribution lens 3, an objective lens 7 is provided at the tip, and a solid-state image sensor 8 is disposed behind the objective lens 7. The electronic scope 100B further includes a switch 10, a scope control unit 9, and a DSP (Digital Signal Processor) 11.

  Under the control of the system controller 1, continuous light is emitted from the light source 31 of the light source unit 3. A rotating plate 36 is disposed in the optical path of continuous light emitted from the light source 31. FIG. 2 is an enlarged view of the rotating plate 36. FIG. 2A is a front view of the rotating plate 36, and FIG. 2B is a side view of the rotating plate 36. The rotating plate 36 has a disk shape centered on the rotating shaft 36a. The rotating plate 36 has an opening 36b and a light shielding part 36c.

  The continuous light emitted from the light source 31 is incident on one end of the light guide 5 only when the opening portion 36b of the rotating plate 36 is in the optical path, and is blocked by the light shielding portion 36c when the light shielding portion 36c is in the optical path. It cannot pass through the rotating plate 36. That is, the continuous light irradiated from the light source 31 is converted into intermittent illumination light (flickering light) that periodically blinks as the rotating plate 36 rotates. The means for converting continuous light into blinking light in this way is not limited to a rotating plate type optical chopper as in this embodiment. For example, a reflection type having a rotating mirror, a shutter using an electro-optical effect such as a liquid crystal cell or a car cell, or a shutter using a magneto-optical effect such as a Faraday effect or a magnetic Kerr effect is used to blink illumination light. It may be used as a means.

  The rotary plate 36 is driven and controlled by the motor control unit 32. Specifically, the rotating plate 36 rotates when the motor control unit 32 drives the motor 34 via the driver 33. An encoder 35 is attached to the rotating plate 36. The encoder 35 has a sensor unit (not shown), and outputs a pulse each time a projection (not shown) provided on the rotating plate 36 crosses the sensor unit. The control of the rotating plate 36 by the motor control unit 32 will be described in detail later.

  The illumination light blinked by the rotary plate 36 propagates through the light guide 5 of the electronic scope 100B, and is emitted from the distal end of the insertion portion flexible tube via the light distribution lens 6. The flickering light reflected by the living tissue in the body cavity enters the solid-state image sensor 8 through the objective lens 7. The solid-state imaging device 8 repeats charge sweeping and transfer periodically under the control of the system controller 1 while accumulating charges according to incident light. Here, sweeping means processing that discards accumulated charges and is not used for image generation. Transfer means a process of outputting accumulated charges as an image signal.

  The image signal output from the solid-state image sensor 8 is input to the DSP 11. The DSP 11 performs predetermined processing on the image signal in order to achieve signal consistency between the electronic scope 100B and the processor 100A. The predetermined processing here includes, for example, clipping processing that limits the dynamic range of the image signal to a predetermined range, and gamma that corrects the γ (gamma) characteristics so that the gradation characteristics and color reproducibility of luminance are appropriate. Correction processing and the like are included. The image signal output from the solid-state imaging device 8 is converted to satisfy the input specifications of the processor 100A by performing these processes in the DSP 11.

  Specifically, the image signal from the solid-state imaging device 8 is sampled and color-separated by the DSP 11 and converted into a luminance signal Y and color difference signals RY and BY. Each signal Y, RY, BY is output to the processor 100A.

  The signals Y, RY, and BY output from the DSP 11 are input to the image processing unit 4 of the processor 100A. The image processing unit 4 performs predetermined processing on the input signals Y, RY, and BY, converts the signals into video signals that conform to the input standard of the monitor 100C, and outputs the video signals to the monitor 100C. The monitor 100C displays an image corresponding to the input video signal.

  Hereinafter, the control process of the motor control unit 32 that controls the rotation frequency of the rotating plate 36, which is a feature of the present invention, will be described in detail. FIG. 3 is a diagram illustrating a configuration of the motor control unit. As shown in FIG. 3, the motor control unit 32 includes a phase comparison unit 32a, a speed comparison unit 32b, and a control switching unit 32c. The phase comparator 32a receives a pulse output from the encoder 35 according to the rotation of the rotary plate 36 and a synchronization signal transmitted from the electronic scope 100B. This synchronization signal is a signal synchronized with a transfer pulse when an image signal is transferred from the DSP 11 to the processor 100A. In the present embodiment, a synchronization signal is transmitted at a frequency of 30 Hz that is synchronized with a transfer pulse of an image signal in an electronic scope including an image sensor with 1 million pixels or more. The phase comparison unit 32a compares the input synchronization signal and the phase of the pulse, and controls the rotation operation of the rotating plate 36 so as to eliminate the phase difference. Thereby, the rotating plate 36 rotates in synchronization with the synchronization signal of the electronic scope 100B.

  The speed comparison unit 32 b receives a pulse output from the encoder 35 according to the rotation of the rotating plate 36 and a frequency instruction value stored in a memory (not shown) of the system controller 1. In the present embodiment, the frequency instruction value is set to 50 Hz or more. This is set in consideration that the blinking frequency of light that humans can perceive as continuous light is approximately 50 Hz or more. That is, the frequency instruction value is set to a frequency higher than the synchronization signal of the electronic scope 100B. In the speed comparison unit 32b, the rotation speed of the rotating plate 36 calculated based on the pulse from the encoder 35 is compared with the speed calculated based on the frequency instruction value, and the rotation is performed so as to eliminate the speed difference between the two. The rotation operation of the plate 36 is controlled. Thereby, the rotating plate 36 rotates at a speed based on a preset frequency instruction value.

  The control switching unit 32c switches which of the phase comparison unit 32a and the speed comparison unit 32b controls the motor driver 33. This switching is performed based on a switching signal output from the system controller 1.

  Next, blinking frequency switching processing including generation of a switching signal output by the system controller 1 will be described with reference to the flowchart of FIG. In this embodiment, when a device other than the electronic scope is connected to the processor 100A, when the operator manually instructs frequency switching, or when a change in the captured image of the electronic scope is not detected, the body cavity by the electronic scope It is assumed that the internal observation is not performed, and control is performed so that the rotating plate 36 is rotated at a frequency of 50 Hz or more. This process is executed by the system controller 1 and is started when the power of the processor 100A is turned on.

  First, in S1, 0 is input as an initial setting value for a parameter N indicating whether or not the electronic scope is connected. N = 1 indicates that an electronic scope is connected, and N = 0 indicates that an electronic scope is not connected. Next, in S2, it is confirmed whether or not an electronic scope is connected to the processor 100A. In the present embodiment, it is determined whether or not the electronic scope is connected by detecting the connection state or the like of the electrical connection unit 101. Specifically, when nothing is electrically connected to the electrical connection unit 101 of the processor 100A, an endoscope other than the electronic scope (for example, a fiberscope) is connected only through the light guide connection unit 5. Judge that it has been.

  FIG. 5 is a flowchart showing a specific electronic scope connection detection process (process S2 in FIG. 4) performed by the scope detection unit 12. First, in S11, the status of the limit switch 15 provided in the processor 100A is confirmed (FIG. 1). The limit switch 15 is a mechanical switch provided inside the connector insertion hole of the electrical connection portion 101. The limit switch 15 transmits a signal indicating that the electronic scope 100B is turned on when the connector of the electronic scope 100B is inserted into the connector insertion hole to the processor 100A, and is turned off when nothing is inserted into the connector insertion hole. Is transmitted to the processor 100A.

  When it is determined that the limit switch 15 is in the OFF state based on the signal from the limit switch 15 (S11: NO), it is determined that the electronic scope is not connected, the process proceeds to S12, and the value of N is set to 0. Is input, and this processing S2 ends. On the other hand, when it is determined that the limit switch 15 is in the ON state (S11: YES), the process proceeds to S13, and communication with the scope control unit 9 is performed.

  The communication here refers to an exchange of endoscope identification data such as a serial number of the electronic scope 100B between the system controller 1 and the scope control unit 9. In continuing S14, it is judged whether communication with the scope control part 9 was successful. Here, the success of communication means that not only the exchange of endoscope identification data is simply executed, but also the system controller 1 is an electronic scope suitable for the blinking frequency switching process of the present embodiment based on the identification data ( For example, it is determined that a megapixel endoscope) is connected. If the communication is successful (S14: YES), it is determined that an electronic scope suitable for the blinking frequency switching process is connected, and 1 is input to N (S15). On the other hand, if the communication is not successful (S14: NO), it is determined that an electronic scope suitable for the blinking frequency switching process is not connected, the process proceeds to S12, and 0 is input to N. When the processes of S15 and S12 are performed, the process S2 ends. In the following text, for the sake of simplicity, an electronic scope suitable for blinking frequency switching processing is simply referred to as an electronic scope unless otherwise specified.

  Returning to FIG. 4, when it is determined in S3 that N = 1, that is, the electronic scope 100B is connected (S3: YES), the process proceeds to S4. On the other hand, if it is determined in S3 that N = 0, that is, the electronic scope 100B is not connected (S3: NO), the system controller 1 instructs to control the rotating plate 36 based on the frequency instruction value. The switching signal to be generated is generated and output to the motor control unit 32 (S8).

  Thus, for example, when the illumination light of the processor 100A enters the eyes of the operator, such as when direct observation is performed with a fiberscope or the like, the rotation frequency of the rotating plate 36 is automatically controlled to be 50 Hz or higher. .

  In S4, it is determined whether or not the frequency switching button 13 is ON. The frequency switch button 13 is provided on a front panel (not shown) provided on the exterior of the processor 100A as shown in FIG. Alternatively, the frequency switching button 13 may be provided on a grip portion (not shown) of the electronic scope 100B. The frequency switching button 13 is manually turned on / off by the operator. When it is determined that the frequency switching button 13 is OFF (S4: NO), the process proceeds to S5. On the other hand, when it is determined that the frequency switching button 13 is ON (S4: YES), the system controller 1 generates a switching signal that instructs to control the rotating plate 36 based on the frequency instruction value. And output to the motor control unit 32 (S8).

  Thereby, when the frequency switching button 13 is ON, it is determined that the operator has instructed frequency switching, and a switching signal for switching the motor control unit 32 is transmitted. Therefore, when the illumination light of the electronic scope 100B is used as illumination for illuminating the lesion removed from the body cavity by the surgeon or the oral cavity before the examination, the surgeon manually turns on the frequency switching button 13. Thus, the rotation frequency of the rotating plate 36 is 50 Hz or more, and the illumination light without flickering is controlled to be emitted from the distal end of the scope.

  Next, in S5, it is determined whether or not there is a change in the captured image sent from the electronic scope 100B. This image change detection process is performed to determine whether the electronic scope 100B is in a state of being used for endoscopic observation or in a state of being not used for observation but placed in an examination room or the like. . FIG. 6 is a flowchart illustrating an image change detection process (S5 in FIG. 4) performed by the image change detection unit 14 that detects a change in an image captured by the electronic scope 100B. In the present embodiment, the change in the image captured by the electronic scope 100B is determined based on the luminance signal Y transmitted from the electronic scope 100B. First, when this process is started, a luminance signal Y1 of one field transferred from the DSP 11 is acquired (S51). And it waits until the signal of the next field is transmitted (S52). Thereafter, when the image signal of the next field is transferred from the DSP 11, the luminance signal Y2 of that field is acquired (S53).

  In subsequent S54, the luminance levels of the luminance signals Y1 and Y2 are compared to calculate a difference value. Next, it is determined whether or not the difference value calculated in S54 is equal to or greater than a predetermined threshold (S55). The threshold value used here is set appropriately as a difference value between luminance levels between fields in which the electronic scope 100B is operated for endoscopic observation and it is determined that the captured image has changed. For example, an endoscope image is acquired for a certain period of time in a state where the electronic scope 100B is actually placed in the examination room under treatment, and the average value of the amount of change in luminance level between adjacent fields in the acquired image is equal to 2 of the standard deviation. A value obtained by adding double (or triple) can be set as the threshold value.

  If the difference value is larger than the threshold value in S55 (S55: YES), it is determined that there is a change in the image captured by the electronic scope 100B (that is, the electronic scope 100B is used for endoscopic observation). Then, 1 is input as the value of the parameter D indicating the change of the captured image (S56). On the other hand, when the difference value is equal to or smaller than the threshold value (S55: NO), it is determined that there is no change in the image acquired by the electronic scope 100B (that is, the electronic scope 100B is not used for endoscopic observation), and imaging is performed. 0 is input as the value of the parameter D indicating the change of the image (S57). After the processes of S56 and S57, the captured image change detection process (S5) ends.

  Next, the process proceeds to S6 of FIG. In S6, if D = 1, that is, if it is determined that the electronic scope 100B is used for endoscopic observation because there is a change in the captured image in the process of S5 (S6: YES), the process proceeds to S7. move on. In S <b> 7, the system controller 1 generates a switching signal that instructs to control the rotating plate 36 based on the synchronization signal, and outputs the switching signal to the motor control unit 32. On the other hand, if D = 0 in S6, that is, if it is determined that the electronic scope 100B is not used for endoscopic observation because there is no change in the captured image in the process of S5 (S6: NO), the process is as follows. Proceed to S8. In S <b> 8, the system controller 1 generates a switching signal that instructs to control the rotating plate 36 based on the frequency instruction value, and outputs the switching signal to the motor control unit 32.

  Thereby, the electronic scope 100B is placed in the examination room in a state where the irradiation light is emitted before and after the examination, and when the blinking light enters directly into the eyes of the operator or the person in the examination room, the rotating plate automatically The rotation frequency of 36 is controlled to be 50 Hz or higher.

  Based on the switching signal output from the system controller 1 by the above processing, the control switching unit 32c of the motor control unit 32 is switched, so that the rotation frequency of the rotating plate and the frequency of the blinking light blinking thereby are switched.

  As described above, the processor 100 </ b> A according to the present embodiment may be used when the electronic scope is not connected (when the fiberscope is connected), when the frequency switching button is turned on by an operator's manual operation, or electronic In each case where a change in the captured image captured by the scope 100B is not detected, it is determined that the flickering light supplied from the processor 100A directly enters the human eye, and the rotation plate 36 is controlled to rotate at a frequency of 50 Hz or more. It is the composition to do. With this configuration, during endoscopic observation with the electronic scope 100B, flickering light synchronized with the image signal transfer pulse from the electronic scope 100B is supplied. On the other hand, when direct observation is performed with a fiberscope or the like, The rotation frequency of the rotating plate 36 is appropriately switched so that blinking light that blinks at a frequency of 50 Hz or higher that is recognized as continuous light is supplied. Thereby, even when flickering light directly enters only humans, discomfort can be prevented without sensing flicker. Furthermore, even when a fiberscope or the like is used, appropriate direct observation can be performed with illumination light without flicker.

  Although the embodiments of the present invention have been described above, the present invention is not limited to these embodiments and can be modified in various ranges. For example, in the light source device in the above embodiment, means for determining each of when the electronic scope is not connected, when the frequency switching button is turned on, and when a change in the captured image of the electronic scope 100B is not detected. Although it is configured to include, at least one of these determination means may be included.

  In the above embodiment, the rotary plate 36 is controlled based on either the synchronization signal of the electronic scope 100B or the frequency instruction value stored in the system controller 1, but the electronic scope 100B controls the processor 100A. When connected, the rotating plate 36 may be controlled based on either the frequency of the synchronization signal from the electronic scope 100B or the frequency obtained by multiplying the frequency of the synchronization signal by an integer.

  FIG. 7 is a diagram illustrating a configuration of the motor control unit 320 in the modified example. 7 is different from the motor control unit 32 in FIG. 3 in that a frequency divider 32d is provided instead of the speed comparison unit 32b. Further, in the motor control unit 320 of FIG. 7, whether the control switching unit 32e inputs the pulse output from the encoder 35 to the phase comparison unit 32a or the output from the frequency divider 32d to the phase comparison unit 32a. Is to be switched.

  The frequency divider 32d is for performing a process of converting the frequency of the pulse output from the encoder 35 to a frequency of 1 / N. The frequency division number N in the frequency divider 32d is set to an arbitrary integer value. In the modification of the present invention described below, the frequency division number N is set to 2.

  FIG. 8 is a flowchart for explaining blinking frequency switching processing including generation of a switching signal in the present modification. This flowchart corresponds to the flowchart of FIG. 4 in the above embodiment. The processor in this modification is assumed to be an electronic scope dedicated device. For this reason, the electronic scope connection is not detected. Accordingly, the flowchart of FIG. 8 differs from the flowchart of FIG. 4 in that it does not include the processes (S1 to S3) relating to the electronic scope connection detection, and the processes of S104 and S105. Also in the present modification, the control switching unit 32e is switched by a switching signal from the system controller 1 as in the above embodiment. Specifically, when it is determined that the normal endoscope observation using the electronic scope is performed (S101: NO and S103: YES), the pulse output from the encoder 35 is input to the phase comparison unit 32a. A switching signal instructing to do so is output (S104). On the other hand, in cases other than the normal endoscope observation (S101: YES or S103: NO), such as when it is determined to be direct observation, the output of the frequency divider 32d is input to the phase comparison unit 32a. An instructing switching unit signal is output (S105).

  When the pulse output from the encoder 35 is input to the phase comparison unit 32a by the control switching unit 32e, the synchronization signal from the electronic scope 100B is detected by the phase comparison unit 32a as in the motor control unit 32 of FIG. The phase difference between the pulses is compared, and the rotation of the rotating plate 36 is controlled so that the phase difference is eliminated. Thereby, in the case of normal body cavity observation, the rotation plate 36 is controlled to rotate in synchronization with the synchronization signal from the electronic scope 100B.

  On the other hand, when the output from the frequency divider 32d is input to the phase comparison unit 32a by the switching unit 32e, the pulse train output from the encoder 35 is converted into a pulse train of 1/2 frequency by the frequency divider 32d. Later, it is input to the phase comparator 32a. Similarly in this case, the phase comparison unit 32a compares the phase difference between the synchronization signal from the electronic scope 100B and the pulse, and controls the rotation of the rotating plate 36 so that the phase difference is eliminated. At this time, in the phase comparison unit 32a, a pulse train having a frequency corresponding to ½ of the frequency at which the rotating plate 36 actually rotates (frequency at which the illumination light blinks) is compared with the synchronization signal by the frequency divider 32d. In this way, the rotation plate 36 is controlled to rotate at a frequency twice that of the synchronization signal by performing control so as to eliminate the phase difference between the synchronization signal and the pulse train of ½ of the blinking frequency. become. Specifically, when the synchronizing signal is 30 Hz, the rotating plate 36 is controlled to rotate at 60 Hz, which is twice that of the synchronizing signal.

  In the above modification, flickering light synchronized with the synchronizing signal from the electronic scope 100B is supplied during normal in-vivo observation, and on the other hand, when direct observation or the like is performed, the frequency is an integral multiple of the synchronizing signal (for example, 60 Hz). It is possible to appropriately switch the rotation frequency of the rotating plate 36 so as to supply the blinking light that blinks in step (3). As a result, even when flickering light directly enters the human eye, the same effect as the above-described embodiment can be obtained in which discomfort can be prevented without detecting flicker. Moreover, since the speed comparison unit is not required as in the above embodiment, the motor control unit can be configured easily.

  In the above modification, the processor is an electronic scope dedicated device, and the electronic scope connection detection process is not provided on the assumption that the electronic scope 100B is connected to the processor 100A. However, the motor control in FIG. By adding the speed comparison unit 32b and the control switching unit 32c of FIG. 3 to the unit 320, the rotation frequency of the rotary plate 36 can be switched depending on the connection state of the electronic scope 100B detected by the electronic scope connection detection process. It becomes.

  Other variations are possible. For example, the connection of the electronic scope 100 </ b> B in the above embodiment is detected based on the status of the limit switch and communication with the scope control unit 9. By performing the connection determination in this manner, the reliability related to the connection detection of the electronic scope suitable for the light source device according to the present invention is made higher. However, the configuration of the endoscope light source device according to the present invention is not limited to this. A configuration may be adopted in which connection is detected by determining only one of the status of the limit switch and the communication with the scope control unit 9. In addition, for example, it is possible to detect the connection of the electronic scope based on the presence or absence of a synchronization signal from the electronic scope 100B.

  In the above embodiment, the frequency switching button 13 is provided on the front panel of the processor 100A or the grip portion of the electronic scope 100B, and the frequency of the rotating plate 36 is switched by manually operating this button. However, the frequency switching function can be simultaneously assigned to a button (for example, a manual dimming setting button) provided on the front panel having another function. In this case, for example, when assigned to the manual dimming setting button, when the manual dimming setting button is operated, the manual dimming setting mode functions and at the same time, switching of the frequency is instructed. Thereby, it is not necessary to provide a separate button for frequency switching, and the number of parts is also reduced.

  Furthermore, in the image change detection process of the captured image of the electronic scope 100B in the above embodiment, the change of the image is detected based on the luminance level of the luminance signal Y. However, the present invention is not limited to this. Various methods can be applied, such as detection based on various parameters of the color difference signal. For example, when a color difference signal is used, an observation tissue in a body cavity generally has a reddish color, and thus, when converted to a primary color signal, red becomes stronger (that is, the color difference signal RY is large). When the signal is output from the electronic scope, it may be configured to determine that the endoscope observation is performed by the electronic scope.

  Further, when the electronic scope is placed in the examination room (outside the body cavity), the image of the electronic scope is illuminated with indoor illumination light that blinks in synchronization with an AC power supply (for example, 50 Hz or 60 Hz) (or image formation). (Not just light and dark) is projected. Utilizing this, by detecting indoor illumination light that blinks at 50 Hz or 60 Hz from the image of the electronic scope, the electronic scope is placed in the body cavity and normal endoscopic observation is performed, or outside the body cavity. It is possible to determine whether or not the flickering light for observing the endoscope is emitted into the indoor space. And you may make it the structure which controls the blinking speed of a rotating plate based on this judgment result. Specifically, the brightness of the image transferred from the electronic scope is repeated (beating) at a frequency of a difference (20 Hz) between a frame rate (for example, 30 Hz) and a blinking cycle (for example, 50 Hz) of a fluorescent lamp. Whether or not the image is obtained by room lighting such as fluorescence is determined based on the frequency of the change in brightness. In addition, for the detection of the room illumination, a sensor for detecting the room illumination light is provided at the tip of the electronic scope 100B, for example, and the electronic scope 100B is taken out of the body cavity based on the detection result of the sensor, and the inside of the room space. It may be determined whether or not blinking light for endoscopic observation is emitted.

1 is a configuration diagram of an electronic endoscope system according to the present invention. FIG. FIG. 2A is an enlarged front view of the rotating plate of the present invention, and FIG. 2B is an enlarged side view of the rotating plate of the present invention. It is a figure which shows the structure of a motor control part. It is a flowchart which shows a blink frequency switching process. It is a flowchart which shows the electronic scope connection detection process in a blink frequency switching process. It is a flowchart which shows the change detection process of the captured image in a blink frequency switching process. It is a figure which shows the structure of the motor control part in the modification of this invention. It is a flowchart which shows the blink frequency switching process in the modification of this invention.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 System controller 2 Timing controller 3 Light source part 4 Image processing part 5 Light guide 9 Scope control part 11 DSP
DESCRIPTION OF SYMBOLS 12 Scope detection part 13 Frequency switching button 14 Image change detection part 15 Limit switch 31 Light source 32 Motor control part 33 Motor driver 34 Motor 35 Encoder 36 Rotating plate 100 Electronic endoscope system 100A Processor 100B Electronic scope 100C Monitor

Claims (9)

An endoscope light source device for supplying illumination light to an endoscope,
Illumination light blinking means that is arranged between a light source and a light guide of the endoscope and periodically blinks the illumination light passing therethrough,
Control means for controlling the illumination light blinking means to blink illumination light at a first frequency based on a signal from the endoscope;
Based on whether a synchronization signal is received from the endoscope, connection detection means for detecting whether the electronic endoscope is connected,
Have
The control means includes
When the connection detection unit does not detect the connection of the electronic endoscope, the illumination light is brightened so that the illumination light is blinked at a second frequency different from the first frequency at which the person does not feel flicker. A light source device for an endoscope, characterized by controlling an extinction means.   The endoscope light source device according to claim 1, wherein the second frequency is higher than the first frequency.   The endoscope light source device according to claim 1, wherein the second frequency is 50 Hz or more.   The endoscope light source device according to any one of claims 1 to 3, wherein the second frequency is an integral multiple of the first frequency. The said connection detection means has a limit switch, and detects whether the electronic endoscope was connected based on the signal from this limit switch, The any one of Claim 1 to 4 characterized by the above-mentioned. Endoscope light source device. The endoscope light source device is:
A manual operation unit for receiving an operation by a user of the endoscope light source device;
The control means controls the illumination light blinking means to blink illumination light at the second frequency when the manual operation unit accepts an operation by the user. To 5. The endoscope light source device according to any one of items 1 to 5 . The endoscope light source device is:
It further comprises image change detection means for detecting a change in the image captured by the electronic endoscope,
The control means controls the illumination light blinking means to blink illumination light at the second frequency when no change in the image is detected by the image change detection means. the endoscope light source device according to any of claims 1 6. The endoscope light source device according to claim 7 , wherein the image change detection unit detects a change in the image based on a luminance signal transmitted from the electronic endoscope. The endoscope light source device according to claim 7 , wherein the image change detection unit detects a change in the image based on a color difference signal transmitted from the electronic endoscope.

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