JP2015104616A - Endoscope system - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an endoscope system which can reduce a fluctuation range of current consumption between a driving period of an imaging part and the other periods.SOLUTION: An endoscope system 1 includes: an imaging part 244 which picks up an image of a subject and generates an image signal of a subject; a driving signal generating part 34 which generates a driving signal to drive the imaging part 244 in a prescribed cycle and outputs the signal to the imaging part 244; a Peltier element 226 as an equivalent load part which has almost the same load as the imaging part 244; and an FPGA (Field Programmable Gate Array) 271 as a control unit which drives the imaging part 244 during a period when the driving signal generating part 34 generates the driving signal and drives the Peltier element 226 while the driving signal generating part 34 does not generate a driving signal.

Description

  The present invention relates to an endoscope system that images the inside of a subject and generates an in-vivo image of the subject.

  Conventionally, in the medical field, an endoscope system is used when observing an organ of a subject such as a patient. An endoscope system has an elongated shape having flexibility, for example, an endoscope (electronic scope) that is inserted into a body cavity of a subject, and an imaging unit that is provided at the tip of an imaging device and captures an in-vivo image And a control device (external processor) that performs predetermined image processing on the in-vivo image captured by the imaging unit, and a display device that can display the in-vivo image subjected to image processing by the control device. When acquiring an in-vivo image using an endoscope system, after inserting the insertion portion into the body cavity of the subject, the imaging unit irradiates the living tissue in the body cavity from the distal end of the insertion portion. In-vivo images are taken. A user such as a doctor observes the organ of the subject based on the in-vivo image displayed by the display device.

  In such an endoscope system, a technique for reducing power consumption consumed by the imaging unit by outputting a driving signal for driving the imaging unit at a predetermined cycle and intermittently driving the imaging unit is known. (See Patent Document 1).

International Publication No. 2012/020709

  However, in Patent Document 1 described above, voltage fluctuations occur due to fluctuations in current consumption during the driving period of the imaging unit and other periods, so high output voltage accuracy is required. There is a problem that adjustment work that takes into account must be performed.

  The present invention has been made in view of the above, and can reduce the range of fluctuations in current consumption during the driving period of the imaging unit and other periods, and can eliminate adjustment work taking voltage fluctuations into account at the time of shipment. An object is to provide an endoscope system.

  In order to solve the above-described problems and achieve the object, an endoscope system according to the present invention includes an endoscope that captures an in-vivo image of a subject by being inserted into a body cavity of the subject, An endoscope system comprising a control device connected to a endoscope so as to be capable of bidirectional communication, an imaging unit that images the subject and generates an image signal of the subject, and the imaging unit A drive signal generation unit that generates a drive signal to be driven at a predetermined cycle and outputs the drive signal to the imaging unit, an equivalent load unit having substantially the same load as the imaging unit, and the drive signal generation unit generates the drive signal And a control unit that drives the equivalent load unit during a period in which the image pickup unit is driven during a period during which the drive signal generation unit does not generate the drive signal.

  In the endoscope system according to the present invention, the endoscope system is connected to the imaging unit and the equivalent load unit, and the output destination of the drive signal is switched to either the imaging unit or the equivalent load unit. A switching unit; and the control unit causes the switching unit to switch the output destination of the driving signal to the imaging unit during a period in which the driving signal generation unit generates the driving signal, while generating the driving signal. The output destination of the drive signal is switched to the equivalent load unit during a period when the unit does not generate the drive signal.

  In the endoscope system according to the present invention, the endoscope system is connected to the power source unit capable of supplying power to the imaging unit and the equivalent load unit, the imaging unit and the equivalent load unit, and the power source unit. A switching unit that switches the electric power supplied from the imaging unit and the equivalent load unit to one of the imaging unit and the equivalent load unit, and the control unit generates the driving signal in the switching unit. The supply destination of the power supply unit is switched to the imaging unit during a period during which the drive signal generation unit is not generating the drive signal while the supply destination of the power supply unit is switched to the equivalent load unit. It is characterized by.

  The endoscope system according to the present invention is the endoscope according to the above invention, wherein the endoscope is connected to an insertion portion whose distal end portion is inserted into a body cavity of a subject and a proximal end portion of the insertion portion, An operation unit that receives an input of an operation signal of the endoscope system; and a connector unit that is detachable from the control device, wherein the drive signal generation unit is provided in the control device, and the imaging unit includes the imaging unit It is provided in a tip part, the switching part is provided in the operation part, and the control part is provided in the connector part.

  In the endoscope system according to the present invention as set forth in the invention described above, the equivalent load portion is a Peltier element provided in contact with the exterior of the operation portion.

  In the endoscope system according to the present invention, in the above invention, the equivalent load portion is provided at the distal end portion, detects the temperature of the imaging unit, and outputs the detection result to the control unit. It is a recording part which records the information regarding a part and / or the said imaging part, It is characterized by the above-mentioned.

  In the endoscope system according to the present invention, in the above invention, the recording unit associates the temperature of the imaging unit with correction information used when correcting the image signal generated by the imaging unit. It is characterized by recording.

  Further, in the endoscope system according to the present invention, in the above invention, the control unit outputs the detection result output from the temperature detection unit during a period in which the drive signal generation unit does not generate the drive signal. The corresponding correction information is obtained from the recording unit.

  According to the endoscope system according to the present invention, it is possible to reduce the fluctuation range of the current consumption during the driving period of the imaging unit and other periods, and to eliminate the adjustment work in consideration of the voltage fluctuation at the time of shipment. There is an effect.

FIG. 1 is a diagram illustrating a schematic configuration of an endoscope system according to the first embodiment of the present invention. FIG. 2 is a block diagram illustrating a functional configuration of a main part of the endoscope system according to the first embodiment of the present invention. FIG. 3 is a timing chart showing the switching timing of the switching unit by the FPGA unit of the endoscope system according to the first embodiment of the present invention. FIG. 4 is a block diagram illustrating a functional configuration of a main part of the endoscope system according to the second embodiment of the present invention. FIG. 5 is a block diagram illustrating a functional configuration of a main part of the endoscope system according to the third embodiment of the present invention. FIG. 6 is a block diagram illustrating a functional configuration of a main part of the endoscope system according to the fourth embodiment of the present invention.

  Hereinafter, as a mode for carrying out the present invention (hereinafter, referred to as “embodiment”), a medical endoscope system that captures and displays an image of a body cavity of a subject such as a patient will be described. The present invention is not limited to the following embodiments. Furthermore, in the description of the drawings, the same portions will be described with the same reference numerals. Furthermore, the drawings are schematic, and it should be noted that the relationship between the thickness and width of each member, the ratio of each member, and the like are different from the actual ones. Moreover, the part from which a mutual dimension and ratio differ also in between drawings. In the following description, an endoscope system will be described as an example of an imaging system.

(Embodiment 1)
FIG. 1 is a diagram illustrating a schematic configuration of an endoscope system according to the first embodiment of the present invention. FIG. 2 is a block diagram illustrating a functional configuration of a main part of the endoscope system according to the first embodiment of the present invention.

  An endoscope system 1 shown in FIGS. 1 and 2 includes an endoscope 2 (endoscope scope) that captures an in-vivo image in a subject by inserting a distal end portion into the body cavity of the subject, The in-vivo image captured by the endoscope 2 is subjected to predetermined image processing, and a control device 3 (processor) that comprehensively controls the operation of the entire endoscope system 1 and illumination light emitted from the distal end of the endoscope 2 And a display device 5 for displaying an in-vivo image subjected to image processing by the control device 3.

  The endoscope 2 includes an insertion portion 21 having an elongated shape having flexibility, an operation portion 22 that is connected to a proximal end side of the insertion portion 21 and receives input of various operation signals, and an insertion portion from the operation portion 22. And a universal cord 23 that includes various cables that extend in a direction different from the direction in which 21 extends and that are connected to the control device 3 and the light source device 4.

  The insertion portion 21 is connected to the distal end portion 24 including an imaging portion 244 described later, a bendable bending portion 25 constituted by a plurality of bending pieces, and a proximal end side of the bending portion 25, and has flexibility. And a long flexible tube portion 26.

  The front end portion 24 is configured using glass fiber or the like, and includes a light guide 241 that forms a light guide path of light emitted from the light source device 4, and an illumination optical system 242 provided at the front end of the light guide 241, or one or more. An optical system 243 that forms an in-vivo image of a subject, and an imaging device that receives the in-vivo image formed by the optical system 243, photoelectrically converts it into an electrical signal, and performs predetermined signal processing The imaging unit 244, the substrate 245 on which the imaging unit 244 is mounted, and a treatment instrument channel (not shown) through which the processing instrument for the endoscope 2 passes.

  The imaging unit 244 continuously generates an analog electrical signal (image signal) by receiving light collected by the optical system 243 and performing photoelectric conversion, and performs predetermined signal processing on the electrical signal. After the application, A / D conversion is performed and output to the control device 3 described later. The imaging unit 244 includes a CCD (Charge Coupled Device) or a CMOS (Complementary) in which a plurality of pixels each having a photodiode that accumulates a charge corresponding to the amount of light and an amplifier that amplifies the charge accumulated by the photodiode are arranged two-dimensionally. (Metal Oxide Semiconductor) etc. The imaging unit 244 outputs a digital image signal (image data) in accordance with a drive signal (drive pulse) input from the control device 3 via the FPGA 271. Note that a control unit that controls driving of the imaging unit 244, a timing generator, and the like may be provided at the distal end portion 24.

  A collective cable 261 in which a plurality of signal lines for transmitting and receiving electrical signals to and from the control device 3 are bundled is connected between the operation unit 22 and the distal end portion 24. An end 261 a on the operation unit 22 side of the collective cable 261 is connected to an operation unit substrate 22 a provided in the operation unit 22. A collective cable 231 is connected between the operation unit 22 and the connector unit 27. The plurality of signal lines include a signal line for transmitting the image signal output from the imaging unit 244 to the control device 3, a signal line for transmitting the control signal and the drive signal output from the control device 3 to the imaging unit 244, and the imaging unit 244. Includes a signal for supplying electric power. Note that the end 261a on the operation unit 22 side of the collective cable 261 is connected to a substrate 262 provided with a connector by solder B1 or the like. Furthermore, the board 262 is connected to a connector (not shown) provided on the operation unit board 22a. Thereby, the collective cable 261 and the operation unit inner substrate 22a can be easily connected.

  In addition, a method of transmitting one signal using two signal lines (differential signal lines) (differential transmission) is used for transmission and reception of electrical signals from the connector unit 27 to the operation unit 22. By making the voltage between the differential signal lines positive (+) and negative (-, phase inversion), even if noise is mixed in each line, it can be canceled. The drive signal can be transferred at high speed. Note that the above-described differential transmission is preferably used when the length of the universal cord 23 and / or the flexible tube portion 26 is long, and when this length is short, the single-end signal transmission using a single-end signal is used. It can be applied even if it exists.

  The operation section 22 includes a bending knob 221 that bends the bending section 25 in the vertical direction and the left-right direction, a treatment instrument insertion section 222 that inserts a treatment instrument such as a biological forceps, a laser knife, and an inspection probe into the body cavity, an air supply unit, It comprises a plurality of first input switches 223a that accept input of signals for switching between water supply means, gas delivery means, and the like, and a plurality of second input switches 223b that accept input of signals for setting the control device 3 or the light source device 4. And an operation switch 223. The treatment tool inserted from the treatment tool insertion portion 222 is exposed from the opening via the treatment tool channel of the distal end portion 24 (not shown).

  The operation unit 22 receives a differential signal as a drive signal input from the connector unit 27 and converts it into a single-ended signal, and a drive signal input from the differential reception amplifier 224. From the first buffer amplifier 225 that amplifies the single-ended signal of the image signal and outputs the amplified signal to the imaging unit 244 of the distal end 24, the Peltier element 226 as an equivalent load unit having a load equivalent to that of the imaging unit 244, and the differential reception amplifier 224 A second buffer amplifier 227 that amplifies a single-ended signal as an input drive signal and outputs the amplified signal to the Peltier element 226, and a differential reception amplifier 224 according to a switching signal input from the FPGA 271 of the connector unit 27 described later. And a switching unit 228 for switching an output destination of a single end signal as an input drive signal.

  The Peltier element 226 is provided with a heat absorption surface in contact with the operation unit inner substrate 22 a and a heat dissipation surface in contact with a metal member 229 provided in the operation unit 22. Accordingly, the Peltier element 226 absorbs heat generated in the operation unit inner substrate 22a, and the absorbed heat is radiated to the exterior 229. As a result, the Peltier element 226 can cool various electric circuits (not shown) such as a power supply circuit provided in the operation unit 22. The Peltier element 226 has substantially the same load as the imaging unit 244. That is, in the first embodiment, the Peltier element functions as an equivalent load unit.

  The switching unit 228 outputs a single-ended signal as a drive signal input from the differential reception amplifier 224 according to a switching signal input from the FPGA 271 of the connector unit 27 to the first buffer amplifier 225 and the second buffer amplifier. Switch to one of 227.

  Further, the operation unit 22 receives a power supply voltage generated by a power supply unit 31 of the control device 3 to be described later via a collective cable 231 and a connector unit 27 together with a ground (GND), and receives an image pickup unit 244 of the distal end portion 24, a differential. The data is output to the reception amplifier 224, the first buffer amplifier 225, and the second buffer amplifier 227. Between the received power source and the ground, a capacitor C1 and a reactance L1 are provided for the loss due to the resistance R1 of the aggregate cable 231 and the power source stabilization. The circuit for supplying signals and power to the endoscope 2 is galvanically isolated from the secondary (ground). Although not shown, the GND of the endoscope 2 is a patient GND separated from the ground.

  The universal cord 23 includes at least a light guide 241 and a collective cable 231. The universal cord 23 has a connector portion 27 (see FIG. 1) that is detachably attached to the light source device 4. The connector portion 27 has a coiled coil cable 27a extending therein, and has an electrical connector portion 28 that is detachable from the control device 3 at the extending end of the coil cable 27a.

  The connector unit 27 includes an FPGA (Field Programmable Gate Array) 271, a differential output amplifier 272, a REGULATOR 273 (hereinafter referred to as “REG273”), an A / D conversion unit 274, and a digital potentiometers unit 275 (hereinafter referred to as “DPM275”). ”).

  The FPGA 271 converts the drive signal input from the control device 3 into a drive signal having a drive timing suitable for the imaging unit 244 and outputs the drive signal to the differential output amplifier 272. The FPGA 271 receives a digital video signal converted by an analog front-end circuit (not shown) of the imaging unit 244, converts the received signal into a signal suitable for the interface of the control device 3, and outputs the signal to the control device 3. . Further, the FPGA 271 generates a drive signal for the drive signal generation unit 34 to drive the imaging unit 244 by driving the switching unit 228 of the operation unit 22 based on the drive signal input from the control device 3. While the image pickup unit 244 is driven during the period during which the drive signal is generated, the drive signal generation unit 34 drives the Peltier element 226 as an equivalent addition unit during a period when the drive signal for driving the image pickup unit 244 is not generated. Further, the FPGA 271 changes the resistance value of the DPM 275 based on the fluctuation of the power supply voltage value detected by the resistor R3 and converted into a digital signal by the A / D converter 274. The FPGA 271 reduces the width of the current drop by performing feedback control of the voltage fluctuation corresponding to the consumption current. In the first embodiment, the FPGA 271 functions as a control unit.

  The differential output amplifier 272 converts a single-end signal as a drive signal for driving the imaging unit 244 input from the FPGA 271 via the transmission cable into a differential signal and outputs the differential signal to the differential reception amplifier 224.

  The REG 273 receives the power supply voltage generated by the power supply unit 31 of the control device 3 together with the ground, converts the voltage input from the control device 3 into a voltage used by the endoscope 2, and converts the operation unit 22, the FPGA 271 and the differential. Output to the output amplifier 272. Between each part of the connector part 27 and the ground, a capacitor C2 for stabilizing the power supply, a resistor R2, and a DPM 275 are provided. The output voltage value of the REG 273 is determined by the ratio of the resistance values of the resistor R2 and the DPM 275.

  The A / D converter 274 detects the current value of the resistor R3, converts the detection result into a digital signal, and outputs the digital signal to the FPGA 271.

  The DPM 275 can change the resistance value, and changes the resistance value in accordance with an instruction signal that changes the resistance value input from the FPGA 271.

  Next, the configuration of the control device 3 will be described. The control device 3 includes a power supply unit 31, an image processing unit 32, a recording unit 33, a drive signal generation unit 34, and a main control unit 35.

  The power supply unit 31 generates a power supply voltage (VDD) and supplies the generated power supply voltage together with the ground to each part of the endoscope 2 via the connector unit 27 and the universal cord 23.

  The image processing unit 32 performs predetermined image processing on the image signal input from the FPGA 271 and outputs the image signal to the display device 5. Specifically, the image processing unit 32 corrects at least black output for the image signal, optical black (OB) subtraction processing, white balance (WB) adjustment processing for adjusting the color of the image signal, color Matrix calculation processing, gamma correction processing, color reproduction processing, edge enhancement processing, and the like are performed.

  The recording unit 33 corresponds to various programs for operating the endoscope system 1, data including various parameters necessary for the operation of the endoscope system 1, and the image signal subjected to image processing by the image processing unit 32. Record image data. The recording unit 33 records the identification information of the control device 3. Here, the identification information includes unique information (ID) of the control device 3, year, specification information of the main control unit 35, and transmission rate information. The recording unit 33 is realized using a semiconductor memory such as a flash memory or a DRAM (Dynamic Random Access Memory).

  The drive signal generation unit 34 generates a reference clock signal (drive pulse) that serves as a reference for the operation of each component of the endoscope 2 and transmits the reference clock signal (drive pulse) to the imaging unit 244 via the FPGA 271, the collective cable 231, and the collective cable 261. . Note that the drive signal generation unit 34 may be provided in the connector unit 27.

  The main control unit 35 is configured by using a CPU (Central Processing Unit) or the like, and performs drive control of each component including the endoscope 2 and the light source device 4 and input / output control of information with respect to each component. The main control unit 35 causes the drive signal generation unit 34 to transmit a reference clock signal to the imaging unit 244 at a predetermined cycle.

  Next, the configuration of the light source device 4 will be described. The light source device 4 includes a light source 41, a light source driver 42, a rotary filter 43, a drive unit 44, a drive driver 45, and a light source control unit 46.

  The light source 41 is configured using a white LED (Light Emitting Diode), a xenon lamp, or the like, and generates white light under the control of the light source control unit 46.

  The light source driver 42 causes the light source 41 to generate white light by supplying current to the light source 41 under the control of the light source control unit 46. Light generated by the light source 41 is irradiated from the tip of the tip portion 24 via the rotary filter 43, a condenser lens (not shown), and the light guide 241.

  The rotary filter 43 is disposed on the optical path of white light emitted from the light source 41, and rotates to transmit only the light having a predetermined wavelength band through the white light emitted from the light source 41. Specifically, the rotary filter 43 includes a red filter 431, a green filter 432, and a blue filter 433 that transmit light having respective wavelength bands of red light (R), green light (G), and blue light (B). And light shielding masks 431a, 432a, and 433a provided between the filters. The rotary filter 43 rotates to sequentially transmit light having red, green, and blue wavelength bands (for example, red: 600 nm to 700 nm, green: 500 nm to 600 nm, blue: 400 nm to 500 nm), and each illumination. Create a shading period between the periods. Thereby, the light source device 4 sequentially emits one of the red light, the green light, and the blue light that narrows the white light emitted from the light source 41 to the endoscope 2 with the light shielding period interposed therebetween. Dew shading can be controlled.

  The drive unit 44 is configured using a stepping motor, a DC motor, or the like, and rotates the rotary filter 43 with reference to the synchronization signal transmitted from the control device 3. The drive driver 45 supplies a predetermined current to the drive unit 44 under the control of the light source control unit 46.

  The light source control unit 46 controls the amount of current supplied to the light source 41 according to the dimming signal transmitted from the main control unit 35. The light source control unit 46 rotates the rotary filter 43 by driving the drive unit 44 via the drive driver 45 under the control of the main control unit 35.

  The display device 5 has a function of receiving and displaying the in-vivo image generated by the control device 3 via the video cable from the control device 3. The display device 5 is configured using, for example, liquid crystal or organic EL (Electro Luminescence).

  In the endoscope system 1 having the above configuration, the switching timing of the switching unit 228 of the operation unit 22 by the FPGA 271 will be described. FIG. 3 is a timing chart showing the switching timing of the switching unit 228 by the FPGA 271. 3A shows the active period and static period of the drive signal, FIG. 3B shows the switching timing of the switching unit 228 by the FPGA 271, and FIG. 3C shows the driving timing of the Peltier element 226.

  As illustrated in FIG. 3, the FPGA 271 drives the switching unit 228 in a predetermined cycle according to the drive signal, and outputs the drive signal to the imaging unit 244 or the Peltier element 226. Specifically, the FPGA 271 drives the switching unit 228 in accordance with the drive signal to output an active drive signal to the imaging unit 244 during the light shielding period of the imaging unit 244, for example, while the imaging unit 244 is in the exposure engine. In addition, a drive signal is output to the Peltier element 226 during a static period in which active drive is not required. Accordingly, voltage fluctuation can be reduced by driving the Peltier element 226 having substantially the same load as that of the imaging unit 244 during a period when the imaging unit 244 stops driving (static period).

Next, a reduction process for reducing the width of the voltage drop performed by the endoscope 2 will be described.
First, the endoscope 2 detects a power supply voltage fluctuation due to a current consumption fluctuation by the resistor R3 (detection step).
Subsequently, the A / D converter 274 converts the voltage value detected by the resistor R3 into a digital signal and outputs it to the FPGA 271 (conversion step).
Thereafter, the FPGA 271 changes the resistance value of the DPM 275 based on the digital signal input from the A / D conversion unit 274 (resistance value changing step).
The RGE 273 determines the output voltage value based on the ratio between the resistance R2 and the resistance value of the DPM 275 (output voltage value determination step).

  As described above, the endoscope 2 performs the above-described four processes in a predetermined cycle, and the FPGA 271 performs feedback control of the voltage fluctuation due to the fluctuation of the consumption current, so that the width of the voltage drop can be reduced.

  According to the first embodiment of the present invention described above, the FPGA 271 switches the driving signal to the imaging unit 244 during the active period in which the switching unit 228 and the driving signal generation unit 34 generate the driving signal, while the driving signal generation unit The drive signal is switched to the Peltier element 226 during a static period when 34 does not generate a drive signal. As a result, the fluctuation range of the current consumption can be reduced during the driving period of the imaging unit 244 and other periods, and the tolerance of the output voltage can be increased. As a result, the adjustment work in consideration of the voltage fluctuation in the operation unit 22 at the transmission path destination at the time of shipment can be omitted. Note that the reduction of the voltage fluctuation width in the present invention is not limited to the voltage fluctuation of the transmission path destination.

  Further, according to the first embodiment of the present invention, since the Peltier element 226 is brought into contact with the exterior 229 of the operation unit 22, the heat generated in the operation unit substrate 22a can be efficiently released.

  Also, according to the first embodiment of the present invention, the FPGA 271 changes the output voltage by changing the resistance value of the DPM 275 based on the current consumption detected by the A / D converter 274. As a result, the voltage fluctuation corresponding to the current consumption can be feedback controlled, and the voltage fluctuation due to the current fluctuation can be reduced.

(Embodiment 2)
Next, a second embodiment of the present invention will be described. The endoscope system according to the second embodiment is different in the configuration of the distal end portion of the endoscope in the endoscope system according to the first embodiment described above. For this reason, below, the structure of the front-end | tip part of an endoscope is demonstrated. In addition, the same code | symbol is attached | subjected to the structure same as Embodiment 1 mentioned above, and description is abbreviate | omitted.

  FIG. 4 is a block diagram illustrating a functional configuration of a main part of the endoscope system according to the second embodiment of the present invention. An endoscope system 100 shown in FIG. 4 includes a control device 3, a light source device 4, a display device 5, and an endoscope 110. The endoscope 110 includes at least an operation unit 22, a connector unit 27, and a distal end unit 300.

  The tip portion 300 includes a light guide 241, an illumination optical system 242, an optical system 243, an imaging unit 244, a substrate 301, and a recording unit 302. The imaging unit 244 and the recording unit 302 are mounted on the substrate 301.

  The recording unit 302 is configured by using a ROM, a flash memory, or the like, and records various information of the endoscope 110, correction information regarding the imaging unit 244, and identification information (serial number or ID) for identifying the imaging unit 244. Here, the correction information includes pixel defect address information of the imaging unit 244, color characteristic information, sensitivity variation information (including gain variation of the readout transistor), shading information and column (vertical stripe) variation information, and types of pixel defects. (For example, white defect or black defect), pixel correction method (for example, using two types of corrections properly), and the like. In the second embodiment, the recording unit 302 functions as an equivalent load unit having substantially the same load as the imaging unit 244.

  In the endoscope system 100 configured as described above, the FPGA 271 drives the switching unit 228 at a predetermined cycle according to the drive signal, and causes the image pickup unit 244 or the recording unit 302 to output the drive signal. Specifically, the FPGA 271 outputs a switching signal to the switching unit 228 in accordance with the driving signal and outputs the driving signal to the imaging unit 244 during the active period of the driving signal, while the driving signal is recorded in the recording unit 302 during the static period of the driving signal. To output. The recording unit 302 outputs correction information of the imaging unit 244 to the FPGA 271 during the static period. Note that the recording unit 302 may output correction information to the FPGA 271 according to the number of frame rates of the imaging unit 244. Further, the recording unit 302 may output the correction information to the FPGA 271 in a time division manner during the static period of the drive signal.

  According to the second embodiment of the present invention described above, the FPGA 271 controls the switching unit 228 so that the driving signal is output to the imaging unit 244 during the active period in which the driving signal generating unit 34 generates the driving signal. On the other hand, the recording unit 302 is driven in a static period in which the drive signal generation unit 34 does not generate a drive signal. As a result, it is possible to reduce the fluctuation range of the current consumption during the driving period of the imaging unit 244 and other periods.

  Further, according to the second embodiment of the present invention, the FPGA 271 outputs correction information of the imaging unit 244 from the recording unit 302 of the distal end unit 300 during the static period of the drive signal. Thereby, even when the substrate 301 of the tip portion 300 is replaced with another substrate, the image processing unit 32 of the control device 3 can perform optimal image processing on the image capturing unit 244 of the replaced substrate. .

  In the second embodiment of the present invention, the recording unit 302 is mounted on the substrate 301. However, the recording unit 302 may be provided on the substrate 262 or the operation unit internal substrate 22a.

(Embodiment 3)
Next, a third embodiment of the present invention will be described. The endoscope system according to the third embodiment is different in the configuration of the distal end portion and the operation unit of the endoscope in the endoscope system according to the first embodiment described above. For this reason, below, the structure of the front-end | tip part and operation part of an endoscope is demonstrated. In addition, the same code | symbol is attached | subjected to the structure same as Embodiment 1 mentioned above, and description is abbreviate | omitted.

  FIG. 5 is a block diagram illustrating a functional configuration of a main part of the endoscope system according to the third embodiment of the present invention. An endoscope system 400 shown in FIG. 5 includes a control device 3, a light source device 4, a display device 5, and an endoscope 410. The endoscope 410 includes at least a distal end portion 500 and an operation portion 510.

  The distal end portion 500 includes a light guide 241, an illumination optical system 242, an optical system 243, an imaging unit 244, a temperature detection unit 501, a recording unit 502, and a substrate 503. The imaging unit 244, the temperature detection unit 501, and the recording unit 502 are provided by being mounted on the substrate 503.

  The temperature detection unit 501 is provided in the vicinity of the imaging unit 244. The temperature detection unit 501 detects the temperature of the imaging unit 244 and outputs the detection result to the FPGA 271.

  The recording unit 502 is configured using a ROM, a flash memory, or the like, and includes various information of the endoscope 410 and correction information regarding the imaging unit 244, the temperature detected by the temperature detection unit 501, the image processing parameters by the image processing unit 32, and the like. Is recorded with the image processing information associated with and identification information (serial number or ID) for identifying the imaging unit 244. Here, the image processing information is information in which the temperature detected by the temperature detection unit 501 and the image processing parameter of the image data by the image processing unit 32 are associated with each other. In the third embodiment, the temperature detection unit 501 and the recording unit 502 function as an equivalent load unit having substantially the same load as the imaging unit 244. That is, the load obtained by adding the temperature detection unit 501 and the recording unit 502 is substantially the same as the load of the imaging unit 244.

  The operation unit 510 amplifies a single-end signal as a drive signal input from the differential reception amplifier 224, the first buffer amplifier 225, and the differential reception amplifier 224, and outputs the amplified signal to the temperature detection unit 501 of the tip 500. From the second buffer amplifier 511, the third buffer amplifier 512 that amplifies the single-ended signal as the drive signal input from the differential reception amplifier 224 and outputs the amplified signal to the recording unit 502 of the tip 500, and the FPGA 271 of the connector unit 27 Switching to switch the output destination of a single-ended signal as a drive signal input from the differential receiving amplifier 224 to the first buffer amplifier 225 or the second buffer amplifier 511 and the third buffer amplifier 512 in accordance with the input switching signal. Part 513.

  In the endoscope 410 configured as described above, the FPGA 271 drives the switching unit 513 in a predetermined cycle according to the drive signal, and outputs the drive signal to the imaging unit 244 or the temperature detection unit 501 and the recording unit 502. Specifically, the FPGA 271 outputs a switching signal indicating an active period or a static period of the driving signal to the switching unit 513 according to the driving signal, and outputs the driving signal to the imaging unit 244 during the active period of the driving signal. The drive signal is output to the temperature detection unit 501 and the recording unit 502 during the static period. The temperature detection unit 501 outputs temperature information of the imaging unit 244 to the FPGA 271 according to the drive signal.

  Thereafter, the FPGA 271 causes the recording unit 502 to output image processing information corresponding to the temperature information input from the temperature detection unit 501 during the static period of the drive signal. Thereby, the image processing unit 32 can perform image processing corresponding to the temperature of the imaging unit 244 on the image signal. Note that the detection result by the temperature detection unit 501 and the output of the image processing information by the recording unit 502 may be simultaneous, or may be time division.

  According to the third embodiment of the present invention described above, the FPGA 271 controls the switching unit 513, so that the drive signal is output to the imaging unit 244 during the active period in which the drive signal generation unit 34 generates the drive signal. On the other hand, the temperature detection unit 501 and / or the recording unit 502 are driven in a static period in which the drive signal generation unit 34 does not generate a drive signal. As a result, it is possible to reduce the fluctuation range of the current consumption during the driving period of the imaging unit 244 and other periods.

  Further, according to the third embodiment of the present invention, the FPGA 271 outputs the temperature information of the imaging unit 244 detected by the temperature detection unit 501 and the image processing information from the recording unit 502 during the static period of the drive signal. Thereby, the image processing unit 32 can perform image processing suitable for the temperature of the imaging unit 244.

  In the third embodiment of the present invention, the temperature detection unit 501 and the recording unit 502 are provided at the tip portion 500, but only the temperature detection unit 501 may be used. In this case, the recording unit 502 may be provided on any of the operation unit substrate 22 a and the substrate 262 provided in the operation unit 510, or the connector unit 27.

(Embodiment 4)
Next, a fourth embodiment of the present invention will be described. The endoscope system according to the fourth embodiment is different in the configuration of the operation unit of the endoscope in the endoscope system according to the first embodiment described above. For this reason, below, the structure of the operation part of an endoscope is demonstrated. In addition, the same code | symbol is attached | subjected to the structure same as Embodiment 1 mentioned above, and description is abbreviate | omitted.

  FIG. 6 is a block diagram illustrating a functional configuration of a main part of the endoscope system according to the fourth embodiment of the present invention. An endoscope system 600 illustrated in FIG. 6 includes a control device 3, a light source device 4, a display device 5, and an endoscope 610. The endoscope 610 includes at least a distal end portion 24, a connector portion 27, and an operation portion 700.

  The operation unit 700 includes a differential reception amplifier 224, a first buffer amplifier 225, a Peltier element 226, a second buffer amplifier 227, an exterior 229, and a switching unit 710.

The switching unit 710 switches the output destination of the power supply voltage input via the connector unit 27 to one of the first buffer amplifier 225 and the second buffer amplifier 227 in accordance with the switching signal input from the FPGA 271. Specifically, the switching unit 710, when the input switching signal R _lo from FPGA271, while outputting a power supply voltage input from the power supply unit 31 via the connector 27 to the first buffer amplifier 225, switching signal When R _hi is input, the power supply voltage input from the power supply unit 31 via the connector unit 27 is output to the second buffer amplifier 227.

  As described above, the switching unit 710 switches the output destination of the power supply voltage input from the power supply unit 31 to the first buffer amplifier 225 or the second buffer amplifier 227 in accordance with the switching signal from the FPGA 271.

  According to the fourth embodiment of the present invention described above, the FPGA 271 controls the switching unit 710, thereby imaging the power supply voltage from the power supply unit 31 during the active period in which the drive signal generating unit 34 generates the drive signal. While outputting to the unit 244, the power supply voltage from the power supply unit 31 is output to the Peltier element 226 during the static period in which the drive signal generation unit 34 does not generate the drive signal. As a result, it is possible to reduce the fluctuation range of the current consumption during the driving period of the imaging unit 244 and other periods.

In the fourth embodiment of the present invention, an example in which the FPGA 271 switches the output destination of the power supply voltage by the switching signal of the two lines of R _hi and R _lo is shown. However, based on the high / low of the signal level of the single line. Thus, the output destination of the power supply voltage may be switched.

  As described above, the present invention can include various embodiments not described herein, and various design changes and the like can be made within the scope of the technical idea specified by the claims. Is possible.

1, 100, 400, 600 Endoscope system 2, 110, 410, 610 Endoscope 3 Control device 4 Light source device 5 Display device 21 Insertion unit 22,510,700 Operation unit 22a Operation unit substrate 23 Universal code 24,300 , 500 Tip portion 25 Bending portion 26 Flexible tube portion 27 Connector portion 31 Power source portion 32 Image processing portion 33 Recording portion 34 Drive signal generating portion 35 Main control portion 41 Light source 42 Light source driver 43 Rotating filter 44 Drive portion 45 Drive driver 46 Light source Control unit 224 Differential reception amplifier 225 First buffer amplifier 226 Peltier element 227,511 Second buffer amplifier 228,513,710 Switching unit 229 Exterior 231 246 261 Collecting cable 241 Light guide 242 Illumination optical system 243 Optical system 244 Imaging Part 245,30 1,503 Substrate 271 FPGA unit 272 Differential output amplifier 273 REG unit 274 A / D conversion unit 275 DPM unit 302,502 Recording unit 501 Temperature detection unit 512 Third buffer amplifier

Claims (8)

An endoscope system comprising: an endoscope that captures an in-vivo image of a subject by being inserted into a body cavity of the subject; and a control device that is connected to the endoscope so as to be capable of bidirectional communication. There,
An imaging unit that images the subject and generates an image signal of the subject;
A drive signal generation unit that generates a drive signal for driving the imaging unit at a predetermined cycle and outputs the drive signal to the imaging unit;
An equivalent load unit having substantially the same load as the imaging unit;
A control unit that drives the imaging unit while the drive signal generation unit generates the drive signal, and drives the equivalent load unit during a period when the drive signal generation unit does not generate the drive signal; ,
An endoscope system comprising: A switching unit that is connected to the imaging unit and the equivalent load unit, and that switches an output destination of the drive signal to either the imaging unit or the equivalent load unit;
The control unit causes the switching unit to switch the output destination of the drive signal to the imaging unit during a period in which the drive signal generation unit generates the drive signal, while the drive signal generation unit transmits the drive signal. The endoscope system according to claim 1, wherein an output destination of the drive signal is switched to the equivalent load unit during a period in which no generation occurs. A power supply unit capable of supplying power to the imaging unit and the equivalent load unit;
A switching unit that is connected to the imaging unit and the equivalent load unit and switches the power supplied from the power supply unit to either the imaging unit or the equivalent load unit;
Further comprising
The control unit switches the supply destination of the power supply unit to the imaging unit while the drive signal generation unit generates the drive signal in the switching unit, while the drive signal generation unit transmits the drive signal to the switching unit. The endoscope system according to claim 1, wherein a supply destination of the power supply unit is switched to the equivalent load unit during a period when the power generation unit does not occur. The endoscope is
An insertion part in which the tip part is inserted into the body cavity of the subject;
An operation unit connected to a proximal end of the insertion unit and receiving an input of an operation signal of the endoscope system;
A connector part detachably attached to the control device;
Have
The drive signal generation unit is provided in the control device,
The imaging unit is provided at the tip,
The switching unit is provided in the operation unit,
The endoscope system according to claim 2, wherein the control unit is provided in the connector unit.   The endoscope system according to claim 4, wherein the equivalent load portion is a Peltier element provided in contact with an exterior of the operation portion.   The equivalent load unit is a temperature detection unit that is provided at the tip, detects the temperature of the imaging unit, and outputs the detection result to the control unit and / or a recording unit that records information about the imaging unit. The endoscope system according to claim 4.   The endoscope according to claim 6, wherein the recording unit records the temperature of the imaging unit in association with correction information used when correcting the image signal generated by the imaging unit. system.   The control unit acquires the correction information corresponding to the detection result output from the temperature detection unit from the recording unit during a period in which the drive signal generation unit does not generate the drive signal. The endoscope system according to claim 7.

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