JP2018171544A - Endoscope system and operation method thereof - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an endoscope system capable of acquiring an image for calculating living body numerical information by putting an illumination condition and a photography condition for each observation object in the same state when calculating living body numerical information for a plurality of observation objects, and an operation method thereof.SOLUTION: An observation object is illuminated by illumination light. A first still image acquired by imaging the observation object is stored in a still image storage part. A partial still image generation part generates a first partial still image by cutting part of the first still image. A display control part executes control to display a real time image as a moving image in a moving image display region Rx of a monitor 18, and display the first partial still image in a partial still image display region Ry of the monitor 18.SELECTED DRAWING: Figure 5

Description

  The present invention relates to an endoscope system that acquires biological numerical information that contributes to the diagnosis of a lesion, and an operating method thereof.

  In the medical field, diagnosis is generally performed using an endoscope system including a light source device, an endoscope, and a processor device. In the diagnosis using this endoscope system, a doctor observes an image displayed on a monitor and determines whether or not a lesion site. Since such a diagnosis based on an endoscopic image is greatly influenced by the skill level of the doctor, a new diagnosis method that does not depend on the skill level of the doctor is required.

  For example, since there is a correlation between the lesioned part and the amount of hemoglobin, Patent Document 1 describes that the amount of hemoglobin is quantified as IHb (Index of Hemoglobin) and IHb is used for the diagnosis of the lesioned part.

Japanese Patent Laid-Open No. 2003-220019

  In diagnosis using biological numerical information such as IHb, for example, as shown in FIG. 4, biological numerical information of three points of A point, B point, and C point in order from the esophagus side in the stomach to be observed. May be calculated and the values may be compared to determine the degree of progression of the lesion. In this case, if the lighting conditions and shooting conditions at each point, such as the distance to be observed at each point and the amount of illumination light emitted at each point, are different at each point, it will be affected. It becomes difficult to accurately compare the biological numerical information calculated at each point.

  For example, even when the degree of progression of lesions at the points A, B, and C is the same, if the lighting conditions and imaging conditions at each point are different, the biometric information at each point is the same. Therefore, it is difficult to accurately compare the biological numerical information. Therefore, in order to accurately compare the biological numerical information of a plurality of different observation targets, it is possible to obtain an image for calculating biological numerical information by making the illumination conditions and imaging conditions in each observation target the same state. Was demanded.

  The present invention provides an endoscope capable of obtaining an image for calculating biological numerical information by calculating the biological numerical information of a plurality of observation targets while keeping the illumination conditions and photographing conditions in each observation target in the same state. It is an object to provide a system and a method for operating the system.

  An endoscope system according to the present invention includes a light source unit that emits illumination light, an imaging unit that captures an observation target illuminated by the illumination light and acquires a first still image, and a still image storage that stores the first still image. A partial still image generation unit that generates a first partial still image by cutting out a part of the first still image, displays an observation target in a moving image display area, and displays the first partial still image on the display unit A display control unit that performs control.

  The display control unit preferably performs control to display the first partial still image in a partial still image display region different from the moving image display region. The display control unit performs control to superimpose and display the first partial still image in the moving image display area. It is preferable that an identification display for identifying the moving image display is provided at the edge of the first partial still image.

  The imaging unit captures an image when a part corresponding to the first partial still image enters the moving image display area, acquires a second still image, and the still image storage unit stores the second still image, The still image generation unit generates a second partial still image by cutting out a part of the second still image, and the display control unit stops displaying the first partial still image after obtaining the second still image, It is preferable to perform control to start displaying the second partial still image.

  A biological numerical information calculation unit that calculates first biological numerical information from the first still image and calculates second biological numerical information from the second still image, and an emission amount of illumination light emitted when the first still image is acquired Based on the comparison result of the light emission amount comparison unit and the light emission amount comparison unit for comparing the light emission amount of the illumination light emitted when the second still image is acquired, and the first biological numerical information or the second biological numerical information It is preferable to include a numerical value correction unit that corrects at least one of them. It is preferable that the imaging unit captures an image when a part corresponding to the first partial still image enters the moving image display area to obtain a second still image, and the still image storage unit stores the second still image. .

  The operation method of the endoscope system according to the present invention includes a first imaging step in which an imaging unit captures an observation target illuminated with illumination light to obtain a first still image, and a still image storage unit includes a first still image. A first still image storage step, a partial still image generation unit that cuts out a part of the first still image to generate a first partial still image, and a display control unit, And a first display control step for performing a control of displaying an observation target in a moving image display area and displaying a first partial still image on a display unit.

  In the first display control step, it is preferable to perform control for displaying the first partial still image in a partial still image display region different from the moving image display region for image display. In the first display control step, it is preferable to perform control to superimpose and display the first partial still image on the moving image display area where the moving image is displayed. A second imaging step in which the imaging unit performs imaging when a part corresponding to the first partial still image enters the moving image display area to obtain a second still image; and a still image storage unit selects the second still image. A second still image storing step for storing, a second still image generating step for generating a second partial still image by cutting a part of the second still image by a partial still image generating unit, and a display control unit for After the acquisition of the two still images, it is preferable to include a second display control step for performing control to stop displaying the first partial still image and start displaying the second partial still image.

  According to the present invention, even when calculating biological numerical information of a plurality of observation objects, it is possible to obtain an image for calculating biological numerical information with the same illumination conditions and imaging conditions for each observation object. become.

It is an external view of an endoscope system. It is a block diagram which shows the function of the endoscope system of 1st Embodiment. It is a graph which shows the spectrum of purple light V, blue light B, green light G, and red light R. It is explanatory drawing which shows A point, B point, and C point of observation object. It is an image figure of the monitor which displays a moving image and a 1st partial still image in parallel. It is an image figure of the monitor which displays the 1st partial still picture on animation display field Rx. It is a flowchart which shows a series of flows of this invention. It is an image figure of a monitor which displays the 1st still picture and the 1st living body numerical information. It is explanatory drawing which shows the 1st-3rd still image. It is a block diagram which shows the function of the endoscope system of 2nd Embodiment. It is a graph which shows the spectrum of the white light light-emitted in the normal mode of 2nd Embodiment, or the normal mode for a measurement. It is a graph which shows the spectrum of the special light light-emitted in the special mode of 2nd Embodiment or the special mode for a measurement. It is a block diagram which shows the function of the endoscope system of 3rd Embodiment. It is a top view of a rotation filter. It is a block diagram which shows the function of the endoscope system of 4th Embodiment. It is a graph which shows the spectrum of the purple light V, the blue light B, the green light G, and the red light R which are different from FIG.

[First Embodiment]
As shown in FIG. 1, the endoscope system 10 according to the first embodiment includes an endoscope 12, a light source device 14, a processor device 16, a monitor 18, and a console 19. The endoscope 12 is optically connected to the light source device 14 and electrically connected to the processor device 16. The endoscope 12 includes an insertion portion 12a to be inserted into a subject, an operation portion 12b provided at a proximal end portion of the insertion portion 12a, a bending portion 12c and a distal end portion 12d provided at the distal end side of the insertion portion 12a. have. By operating the angle knob 12e of the operation unit 12b, the bending unit 12c performs a bending operation. With this bending operation, the tip 12d is directed in a desired direction. The “display unit” of the present invention corresponds to the monitor 18.

  In addition to the angle knob 12e, the operation unit 12b is provided with a mode switching SW 13a, a freeze button 13b, and a zoom operation unit 13c. The mode switching SW 13a is used for switching operation between four types of modes: a normal mode, a special mode, a normal mode for measurement, and a special mode for measurement. The normal mode is a mode for displaying a normal image on the monitor 18. The special mode is a mode for displaying a special image on the monitor 18. The normal mode for measurement is a mode in which biological numerical information is calculated and displayed on the monitor 18 when a still image of a normal image is acquired. The special measurement mode is a mode in which biological numerical information is calculated and displayed on the monitor 18 when a still image of the special image is acquired.

  The freeze button 13b is used when acquiring a still image to be observed. By pressing the freeze button 13b, a still image acquisition instruction is transmitted to the light source device 14 and the processor device 16, and the still image to be observed at that time is recorded in the still image storage unit 72. The zoom operation unit 13c is used when performing magnified observation for magnifying and observing an observation target. By operating the zoom operation unit 13c, the zoom lens 47 (see FIG. 2) moves between the tele position and the wide position.

  The processor device 16 is electrically connected to the monitor 18 and the console 19. The monitor 18 outputs and displays image information and the like. The console 19 functions as a UI (User Interface) that receives input operations such as function settings. The processor device 16 may be connected to an external recording unit (not shown) for recording image information and the like.

  As shown in FIG. 2, the light source device 14 includes a V-LED (Violet Light Emitting Diode) 20a, a B-LED (Blue Light Emitting Diode) 20b, a G-LED (Green Light Emitting Diode) 20c, and an R-LED (Red). Light Emitting Diode) 20d, a light source control unit 21 that controls driving of the four color LEDs 20a to 20d, and an optical path coupling unit 23 that couples the optical paths of the four color lights emitted from the four color LEDs 20a to 20d. . The light coupled by the optical path coupling unit 23 is irradiated into the subject through a light guide (LG (Light Guide)) 41 and an illumination lens 45 inserted into the insertion unit 12a. An LD (Laser Diode) may be used instead of the LED. The above-mentioned “four-color LEDs 20a to 20d” correspond to the “light source section” of the present invention.

  As shown in FIG. 3, the V-LED 20a generates purple light V having a center wavelength of 405 ± 10 nm and a wavelength range of 380 to 420 nm. The B-LED 20b generates blue light B having a center wavelength of 460 ± 10 nm and a wavelength range of 420 to 500 nm. The G-LED 20c generates green light G having a wavelength range of 480 to 600 nm. The R-LED 20d generates red light R having a center wavelength of 620 to 630 nm and a wavelength range of 600 to 650 nm. Note that it is not necessary to use all four colors of light for the illumination of the observation target. For example, the observation object may be illuminated with light of three colors, blue light B, green light G, and red light R.

  As shown in FIG. 2, the light source control unit 21 operates in the normal mode, the special mode, the normal mode for measurement, and the special mode for measurement in any of the observation modes V-LED 20a, B-LED 20b, G-LED 20c. The R-LED 20d is turned on. Accordingly, the observation target is irradiated with light in which four colors of light of purple light V, blue light B, green light G, and red light R are mixed. In the light source controller 21, the light quantity ratio among the violet light V, blue light B, green light G, and red light R is set to be different between the normal observation mode and the special observation mode. In the normal observation mode, the LEDs 20a to 20d are controlled so that the light quantity ratio becomes Vc, Bc, Gc, and Rc. In the special observation mode, the LEDs 20a to 20d are controlled so that the light quantity ratio becomes Vs, Bs, Gs, and Rs.

  The light guide 41 is built in the endoscope 12 and the universal cord (the cord connecting the endoscope 12, the light source device 14, and the processor device 16), and the light coupled by the optical path coupling unit 23 is viewed in the endoscope. It propagates to the tip 12d of the mirror 12. A multimode fiber can be used as the light guide 41. As an example, a thin fiber cable having a core diameter of 105 μm, a cladding diameter of 125 μm, and a diameter of φ0.3 to 0.5 mm including a protective layer serving as an outer shell can be used.

  The distal end portion 12d of the endoscope 12 is provided with an illumination optical system 30a and an imaging optical system 30b. The illumination optical system 30 a has an illumination lens 45, and light from the light guide 41 is irradiated to the observation target via the illumination lens 45. The imaging optical system 30 b includes an objective lens 46, a zoom lens 47, and an imaging sensor 48. Reflected light from the observation target enters the image sensor 48 through the objective lens 46 and the zoom lens 47. As a result, a reflected image of the observation object is formed on the image sensor 48.

  The imaging sensor 48 (corresponding to the “imaging unit” of the present invention) is a color imaging sensor, which captures a reflection image of a subject and outputs an image signal. Based on the output image signal, a still image (in this embodiment, a first still image, a second still image, and a third still image) and a moving image are generated. The image sensor 48 is preferably a CCD (Charge Coupled Device) image sensor, a CMOS (Complementary Metal-Oxide Semiconductor) image sensor, or the like. The image sensor 48 used in the present invention is a color image sensor for obtaining RGB image signals of three colors of R (red), G (green), and B (blue), that is, an R pixel provided with an R filter. , A so-called RGB imaging sensor including a G pixel provided with a G filter and a B pixel provided with a B filter.

  The image sensor 48 is a so-called complementary color image sensor that includes complementary filters for C (cyan), M (magenta), Y (yellow), and G (green) instead of an RGB color image sensor. May be. When the complementary color imaging sensor is used, CMYG four-color image signals are output. Therefore, it is necessary to convert CMYG four-color image signals into RGB three-color image signals by complementary color-primary color conversion. . Further, the image sensor 48 may be a monochrome image sensor not provided with a color filter. In this case, the light source control unit 21 needs to turn on the blue light B, the green light G, and the red light R in a time-sharing manner, and add a synchronization process in the processing of the imaging signal.

  The image signal output from the image sensor 48 is transmitted to the CDS / AGC circuit 50. The CDS / AGC circuit 50 performs correlated double sampling (CDS (Correlated Double Sampling)) and automatic gain control (AGC (Auto Gain Control)) on an image signal which is an analog signal. The image signal that has passed through the CDS / AGC circuit 50 is converted into a digital image signal by an A / D converter (A / D (Analog / Digital) converter) 52. The A / D converted digital image signal is input to the processor device 16.

  The processor device 16 includes a receiving unit 53, a DSP (Digital Signal Processor) 56, a noise removing unit 58, a first switching unit 60, a normal image processing unit 62, a special image processing unit 64, and a second switching unit. 66, a display control unit 68, a still image storage unit 72, a partial still image generation unit 74, a biological numerical value information calculation unit 76, a light emission amount comparison unit 78, and a numerical value correction unit 80.

  The receiving unit 53 receives a digital RGB image signal from the endoscope 12. The R image signal corresponds to a signal output from the R pixel of the imaging sensor 48, the G image signal corresponds to a signal output from the G pixel of the imaging sensor 48, and the B image signal is output from the B pixel of the imaging sensor 48. Corresponds to the signal to be transmitted.

  The DSP 56 performs various signal processing such as defect correction processing, offset processing, gain correction processing, linear matrix processing, gamma conversion processing, and demosaicing processing on the received image signal. In the defect correction process, the signal of the defective pixel of the image sensor 48 is corrected. In the offset process, the dark current component is removed from the RGB image signal subjected to the defect correction process, and an accurate zero level is set. In the gain correction process, the signal level is adjusted by multiplying the RGB image signal after the offset process by a specific gain. The RGB image signal after the gain correction process is subjected to a linear matrix process for improving color reproducibility. After that, brightness and saturation are adjusted by gamma conversion processing. The RGB image signal after the linear matrix processing is subjected to demosaic processing (also referred to as isotropic processing or pixel interpolation processing), and a signal of a color that is insufficient at each pixel is generated by interpolation. By this demosaic processing, all the pixels have RGB signals.

  The noise removing unit 58 removes noise from the RGB image signal by performing noise removal processing (for example, a moving average method, a median filter method, etc.) on the RGB image signal subjected to gamma correction or the like by the DSP 56. The RGB image signal from which noise has been removed is transmitted to the first switching unit 60.

  When the normal mode or the normal mode for measurement is set by the mode switching SW 13a, the first switching unit 60 transmits the RGB image signal to the normal image processing unit 62 and sets the special mode or the special mode for measurement. If it is, the RGB image signal is transmitted to the special image processing unit 64.

  The normal image processing unit 62 performs color conversion processing, color enhancement processing, and structure enhancement processing on the RGB image signal. In the color conversion process, a 3 × 3 matrix process, a gradation conversion process, a three-dimensional LUT process, and the like are performed on the digital RGB image signal to convert the digital RGB image signal into a color converted RGB image signal. Next, various color enhancement processes are performed on the RGB image signal that has been subjected to the color conversion process. A structure enhancement process such as spatial frequency enhancement is performed on the RGB image signal that has been subjected to the color enhancement process. The RGB image signal subjected to the structure enhancement process is input from the normal image processing unit 62 to the second switching unit 66 as an RGB image signal of the normal image.

  As with the normal image processing unit 62, the special image processing unit 64 performs color conversion processing, color enhancement processing, and structure enhancement processing on the RGB image signal. These processed RGB image signals are input from the special image processing unit 64 to the second switching unit 66 as RGB image signals of the special image.

  The second switching unit 66 transmits the RGB image signal of the normal image to the display control unit 68 unless receiving a still image acquisition instruction from the freeze button 13b. When a still image acquisition instruction is received, an RGB image signal of a normal image or a special image is transmitted to the still image storage unit 72. When the normal mode or the special mode is set, the display control unit 68 performs display control so that the normal image or the special image is displayed on the monitor 18 based on the RGB image signal of the normal image or the special image. . On the other hand, when the measurement normal mode or the measurement special mode is set, the display control unit 68 is based on the normal image or the RGB image of the special image and the partial still image generated by the partial still image generation unit 74. Thus, display control is performed so that the normal image or the special image and the partial still image are displayed on the monitor 18. This display control will be described later.

  The still image storage unit 72 stores the still image transmitted from the second switching unit 66 when the freeze button 13b is operated. In the present embodiment, as the still images stored in the still image storage unit 72, the first still image acquired by imaging the point A among the observation objects shown in FIG. 4 and the point B adjacent to the point A are captured. The second still image acquired in this way and the third still image acquired by imaging the point C adjacent to the point B are included.

  The partial still image generation unit 74 cuts out a part of the still image stored in the still image storage unit 72 and generates a partial still image. In the present embodiment, when the first still image is stored in the still image storage unit 72 by imaging the point A to be observed, the partial still image generation unit 74 cuts a part of the first still image and A one-part still image is generated. The generated first partial still image is transmitted to the display control unit 68.

  After the first still image is acquired, the display control unit 68 displays the moving image display area Rx in the center on the monitor 18 until the freeze button 13b is operated and the second still image is acquired as shown in FIG. While displaying a normal image or a special image as a moving image, the first partial still image is displayed in a partial still image display region Ry provided on the side of the moving image display region Rx. The doctor observes both the moving image display and the first partial still image displayed on the monitor 18, and operates the freeze button 13b when the portion corresponding to the point B and the second partial still image enters the moving image display region Rx. To do. As a result, the second still image including the point B and the first partial still image is stored in the still image storage unit 72. If the first partial still image is not displayed on the monitor 18 together with the moving image, it is extremely difficult to acquire the second still image so as to include the first partial still image.

  As described above, since the second still image includes the first partial still image that is a common part with the first still image, at least the first partial still image is the first still image or the second still image. For a certain portion, the distance to the observation target is the same, and the amount of reflected light from the observation target is also the same. Therefore, it is possible to make the illumination condition and shooting condition when the first still image is acquired substantially the same as the illumination condition and shooting condition when the second still image is acquired.

  The partial still image generation unit 74 acquires a second still image including the point B and the first partial still image, and cuts off a part of the second still image when stored in the still image storage unit 72. A second partial still image is generated. The generated second partial still image and the moving image of the normal image or the special image are displayed on the monitor 18. Then, when the point corresponding to the next observation point C and the part corresponding to the second partial still image enter the moving image display region Rx and the doctor operates the freeze button 13b, the point C and the second partial still image are included. The third still image is stored in the still image storage unit 72. Since the third still image includes the second partial still image that is a common part with the second still image, the third still image is acquired with the illumination conditions and the shooting conditions when the second still image is acquired. The lighting conditions and shooting conditions are almost the same.

  Instead of displaying the partial still image in the partial still image display region Ry, the partial still image may be displayed superimposed on the moving image display region Rx. In this case, it is preferable that the partial still image is provided with an identification display for identification from the moving image display. For example, as shown in FIG. 6, when the first partial still image is superimposed on the moving image display area Rx and displayed as a moving image, identification blinking is performed as an identification display at the edge of the first partial still image at regular intervals. It is preferable to provide the line La.

  The biological numerical information calculation unit 76 calculates biological numerical information based on the still image stored in the still image storage unit 72. The calculated biological numerical information is displayed on the monitor 18. In the present embodiment, the first biological value information is calculated from the first still image, the second biological value information is calculated from the second still image, and the third biological value information is calculated from the third still image. Here, the lighting conditions and shooting conditions when the first still image is acquired, the lighting conditions and shooting conditions when the second still image is acquired, and the lighting conditions and shooting conditions when the third still image is acquired Are substantially the same, the first to third biological numerical information obtained from the first to third still images, even if there is a difference in their numerical values, This is not due to differences in imaging conditions, but due to differences based on biological factors such as the degree of lesion progression. Thereby, the first to third biological numerical information can be accurately compared.

As the biological numerical information, it is preferable to calculate a hemoglobin index (IHb), oxygen saturation, blood vessel depth, blood vessel density, and the like. For example, the hemoglobin index is calculated based on the following formula.
(Formula): IHb = 32 × Log ₂ (Rx / Gx)
However, “Rx” represents the pixel value of the R image signal of the still image, and “Gx” represents the pixel value of the G image signal of the still image.

  The light emission amount comparison unit 78 compares the light emission amount of the illumination light emitted when a still image at a certain point is acquired with the light emission amount of illumination light emitted when a still image at another point is acquired. In the present embodiment, the first total light emission amount for the four colors of purple light V, blue light B, green light G, and red light R emitted when the first still image is acquired, and the second still image are acquired. The first total comparison result is output by comparing the second total light emission amounts for the four colors of purple light V, blue light B, green light G, and red light R emitted at times. Also, the second total light emission amount is compared with the third total light emission amount for the four colors of purple light V, blue light B, green light G, and red light R emitted when the third still image is acquired. The second comparison result is output. The first to third total light emission amounts are stored in a light emission amount storage unit provided in either the light source device 14 or the processor device 16.

  The numerical value correcting unit 80 corrects the biological numerical value information based on the comparison result in the light emission amount comparing unit 78. In the present embodiment, at least one of the first biological numerical information or the second biological numerical information is corrected based on the first comparison result, and the second biological numerical information or the third biological numerical information is determined based on the second comparison result. Correct at least one of the following. For example, when the first total light emission amount and the second total light emission amount are different, the first biological value information or the second biological value is determined according to the difference between the first total light emission amount and the second total light emission amount. Correct at least one of the information. When the first total light emission amount and the second total light emission amount are the same, it is not necessary to correct the first or second biological value information.

  Next, a series of flows for obtaining the first to third still images at the points A, B, and C to be observed and calculating the first to third biological numerical information from the first to third still images. This will be described with reference to the flowchart of FIG. First, the normal mode is set, and the insertion portion 12a of the endoscope 12 is inserted into the sample. When the distal end portion 12d of the insertion portion 12a reaches the point A to be observed, the mode switching SW 13a is operated to switch from the normal mode to the measurement normal mode or the measurement special mode.

  Next, the first still image is acquired by pressing the freeze button 13b and imaging the point A. The first still image is stored in the still image storage unit 72. The biological numerical information calculation unit 76 calculates first biological numerical information based on the first still image. As shown in FIG. 8, the display control unit 68 controls the moving image display area Rx of the monitor 18 to display the first still image continuously for several seconds and to display the first biological value information. . After the continuous display of the first still image, the partial still image generation unit 74 generates a first partial still image by cutting a part of the first still image. Then, the display control unit 68 performs control to display the normal image or the special image moving image in the moving image display region Rx and to display the first partial still image in the partial still image display region Ry.

  The doctor observes both the moving image display and the first partial still image displayed on the monitor 18, and when the site corresponding to the next observation target point B and the first partial still image enters the moving image display region Rx. Then, the freeze button 13b is pressed. Thereby, the 2nd still picture containing B point and the 1st partial still picture is obtained. The second still image is stored in the still image storage unit 72. The biological numerical information calculation unit 76 calculates second biological numerical information based on the second still image. The numerical value correcting unit 80 also includes the first total light emission amount of the purple light V, the blue light B, the green light G, and the red light R when acquiring the first still image, and the purple light V and blue when acquiring the second still image. From the comparison result with the second total light emission amount of the light B, the green light G, and the red light R, the second biological value information is corrected. The corrected second biological value information is continuously displayed for several seconds together with the second still image.

  After continuous display of the second biological value information and the second still image, a moving image is displayed in the moving image display area Rx of the monitor 18, and a second partial still image is displayed in the partial still image display area Ry. The second partial still image is generated by cutting out a part of the second still image. In the same manner, the doctor presses the freeze button 13b when the point C, which is the next observation target, and the part corresponding to the second partial still image enter the moving image display region Rx. Thereby, the 3rd still picture containing C point and the 2nd partial still picture is obtained. The third still image is stored in the still image storage unit 72. In the same manner as described above, the third biological numerical information is calculated from the third still image, and the third biological numerical information is corrected by the numerical correction unit 80. The corrected third biological numerical information is continuously displayed for several seconds together with the third still image.

  After the continuous display of the third still image, the first to third still images and the first to third still images in the first to third still images as shown in FIG. To third biological numerical information are displayed in a list on the monitor 18. The doctor makes a diagnosis such as to which point the lesion has progressed by comparing the first to third biological numerical information.

  Here, among the first to third still images, the first still image and the second still image have the first partial still image as a common part image, so observation at the time of acquiring the first still image Since the distance and the observation distance at the time of acquiring the second still image are substantially the same, and the second still image and the third still image have the second partial still image as a common part image, the second still image The observation distance at the time of image acquisition and the observation distance at the time of acquisition of the third still image are substantially the same. Accordingly, since the illumination conditions and the shooting conditions when the first to third still images are acquired are almost the same, the first to third biological numerical information obtained from the first to third still images are accurately obtained. Can be compared.

  Among the calculated first to third biological numerical information, for the second biological numerical information, purple light V, blue light B, green light G, and red light emitted when the first and second still images are acquired. The correction is made based on the result of comparing the first and second total light emission amounts of R, and for the third biological value information, purple light V and blue light emitted when the second and third still images are acquired. Correction is performed based on the result of comparing the second and third total light emission amounts of the light B, the green light G, and the red light R. Therefore, even if the first to third total light emission amounts are different, the first to third biological value information is corrected so that there is no error in the biological value information based on the first to third total light emission amounts. Thus, the corrected first to third biological value information can be compared more accurately than the first to third biological value information before correction.

[Second Embodiment]
In the second embodiment, the observation target is illuminated using a laser light source and a phosphor instead of the four-color LEDs 20a to 20d shown in the first embodiment. The rest is the same as in the first embodiment.

  As shown in FIG. 10, in the endoscope system 100, in the light source device 14, a blue laser light source (“445LD” in FIG. 10) that emits blue laser light having a central wavelength of 445 ± 10 nm instead of the four color LEDs 20a to 20d. 104) and a blue-violet laser light source (denoted as “405LD” in FIG. 10) 106 that emits a blue-violet laser beam having a center wavelength of 405 ± 10 nm is provided. Light emission from the semiconductor light emitting elements of these light sources 104 and 106 is individually controlled by the light source control unit 108, and the light quantity ratio between the emitted light of the blue laser light source 104 and the emitted light of the blue-violet laser light source 106 is freely changeable. It has become.

  The light source control unit 108 drives the blue laser light source 104 in the normal mode and the measurement normal mode. On the other hand, in the special mode and the measurement special mode, both the blue laser light source 104 and the blue-violet laser light source 106 are driven, and the emission ratio of the blue laser light is higher than the emission ratio of the blue-violet laser light. It is controlled to become larger. The laser light emitted from each of the light sources 104 and 106 enters the light guide (LG) 41 through optical members (all not shown) such as a condenser lens, an optical fiber, and a multiplexer.

  Note that the full width at half maximum of the blue laser beam or the blue-violet laser beam is preferably about ± 10 nm. As the blue laser light source 104 and the blue-violet laser light source 106, a broad area type InGaN laser diode can be used, and an InGaNAs laser diode or a GaNAs laser diode can also be used. The light source may be configured to use a light emitter such as a light emitting diode.

  In addition to the illumination lens 45, the illumination optical system 30a is provided with a phosphor 110 on which blue laser light or blue-violet laser light from the light guide 41 is incident. When the phosphor 110 is irradiated with the blue laser light, the phosphor 110 emits fluorescence. Some of the blue laser light passes through the phosphor 110 as it is. The blue-violet laser light is transmitted without exciting the phosphor 110. The light emitted from the phosphor 110 is irradiated into the specimen through the illumination lens 45. In the second embodiment, the configuration including the blue laser light source 104, the blue-violet laser light source 106, and the phosphor 110 corresponds to the “light source unit” of the present invention.

  Here, in the normal mode and the normal mode for measurement, since the blue laser light is mainly incident on the phosphor 110, the blue laser light and the fluorescence excited and emitted from the phosphor 110 by the blue laser light as shown in FIG. The observation target is irradiated with white light that is combined. On the other hand, in the special mode and the measurement special mode, since both the blue-violet laser beam and the blue laser beam are incident on the phosphor 110, the blue-violet laser beam, the blue laser beam, and the blue laser as shown in FIG. Special light obtained by combining the fluorescence excited and emitted from the phosphor 110 by light is irradiated into the specimen.

The phosphor 110 absorbs a part of the blue laser light and emits a plurality of types of phosphors that emit green to yellow light (for example, YAG phosphors or phosphors such as BAM (BaMgAl ₁₀ O ₁₇ )). It is preferable to use what is comprised including. If a semiconductor light emitting element is used as an excitation light source for the phosphor 110 as in this configuration example, high intensity white light can be obtained with high luminous efficiency, and the intensity of white light can be easily adjusted, and the color of white light can be easily adjusted. Changes in temperature and chromaticity can be kept small.

  In the second embodiment, the light emission amount comparison unit 78 compares the light emission amount at the time of acquiring the first still image with the light emission amount at the time of acquiring the second still image, or at the time of acquiring the second still image. When comparing the light emission amount with the light emission amount at the time of acquiring the third still image, the light emission amount at the time of acquiring the first to third still images is the AE (Auto Exposure) value obtained at the time of acquiring the first to third still images. It is preferable to use the one calculated based on the above. The AE value is calculated from the RGB image signal obtained when the first to third still images are acquired.

[Third Embodiment]
In the third embodiment, the observation target is illuminated using a broadband light source such as a xenon lamp and a rotary filter instead of the four-color LEDs 20a to 20d shown in the first embodiment. In this case, instead of the color image sensor 48, the observation target is imaged by a monochrome image sensor. The rest is the same as in the first embodiment.

  As shown in FIG. 13, in the endoscope system 200, in the light source device 14, instead of the four color LEDs 20a to 20d, a broadband light source 202, a diaphragm 203, a rotary filter 204, a filter switching unit 205, and a light source control unit 208 are provided. Is provided. The imaging optical system 30b is provided with a monochrome imaging sensor 206 that is not provided with a color filter, instead of the color imaging sensor 48.

  The broadband light source 202 is a xenon lamp, a white LED, or the like, and emits white light having a wavelength range from blue to red. The rotary filter 204 includes a normal mode filter 208 provided inside and a special mode filter 209 provided outside (see FIG. 14). The filter switching unit 205 moves the rotary filter 204 in the radial direction. When the mode switching SW 13a sets the normal mode or the normal mode for measurement, the filter switching unit 205 sets the normal mode filter 208 of the rotary filter 204 to white light. When inserted into the optical path and set to the special mode or the measurement special mode, the special mode filter 209 of the rotary filter 204 is inserted into the optical path of white light. In the third embodiment, the configuration including the broadband light source 202 and the rotation filter 204 corresponds to the “light source unit” of the present invention. The diaphragm 203 is controlled by the light source control unit 208, and the amount of white light incident on the rotary filter 203 is adjusted by adjusting the diaphragm 203.

  As shown in FIG. 14, the normal mode filter 208 includes a B filter 208a that transmits blue light of white light, a G filter 208b that transmits green light of white light, and white light along the circumferential direction. Among them, an R filter 208c that transmits red light is provided. Therefore, in the normal mode or the normal mode for measurement, the rotation filter 204 rotates, so that blue light, green light, and red light are alternately irradiated on the observation target.

  The special mode filter 209 includes a B filter 209a that transmits special blue light having a wavelength band different from that of the B filter 208a in white light and a special filter having a wavelength band different from that of the G filter 208b in white light along the circumferential direction. A G filter 209b that transmits green light and an R filter 209c that transmits special red light having a wavelength band different from that of the R filter 208c among white light are provided. Therefore, in the special mode or the measurement special mode, the rotation filter 204 is rotated so that the special blue light, the special green light, and the special red light are alternately irradiated on the observation target.

  In the endoscope system 200, in the normal mode and the normal mode for measurement, the inside of the specimen is imaged by the monochrome imaging sensor 206 every time blue light, green light, and red light are irradiated on the observation target. Thereby, RGB image signals of three colors are obtained. Based on the RGB image signals, a normal image is generated by the same method as in the first embodiment.

  On the other hand, in the special mode and the measurement special mode, the monochrome imaging sensor 206 images the inside of the specimen every time the observation object is irradiated with special blue light, special green light, and special red light. Thereby, RGB image signals of three colors are obtained. Based on these RGB image signals, a special image is generated by the same method as in the first embodiment.

  In the third embodiment, the light emission amount comparison unit 78 compares the light emission amount at the time of acquiring the first still image with the light emission amount at the time of acquiring the second still image, or at the time of acquiring the second still image. When comparing the light emission amount with the light emission amount at the time of acquiring the third still image, the light emission amount at the time of acquiring the first to third still images is the AE (Auto Exposure) value obtained at the time of acquiring the first to third still images. It is preferable to use the one calculated based on the above. Here, as in the second embodiment, the AE value is calculated from the RGB image signals obtained at the time of obtaining the first to third still images.

[Fourth Embodiment]
In the fourth embodiment, the observation target is illuminated using a broadband light source such as a xenon lamp instead of the four-color LEDs 20a to 20d shown in the first embodiment. The rest is the same as in the first embodiment.

  As shown in FIG. 15, in the endoscope system 300, the light source device 14 is provided with a broadband light source 202, a diaphragm 203, and a light source control unit 208 similar to those of the third embodiment, instead of the four-color LEDs 20a to 20d. It has been. White light emitted from the broadband light source 202 is applied to the observation target through the diaphragm 203, the light guide 41, and the illumination lens 45. In the fourth embodiment, the configuration including the broadband light source 202 corresponds to the “light source unit” of the present invention.

  In the endoscope system 300, in the normal mode and the normal mode for measurement, the observation target is illuminated with white light adjusted to the normal mode light amount by the diaphragm 202, and the color imaging sensor 48 images the observation target. Based on the RGB image signals obtained by this imaging, a normal image is generated by a method substantially similar to that of the first embodiment. On the other hand, in the special mode and the measurement special mode, the observation target is illuminated with white light adjusted to the special mode light amount by the diaphragm 202, and the observation target is imaged by the color imaging sensor 48. Based on the RGB image signals obtained by this imaging, a special image is generated by a method almost the same as in the first embodiment.

  In the fourth embodiment, the light emission amount comparison unit 78 compares the light emission amount at the time of acquiring the first still image and the light emission amount at the time of acquiring the second still image, or the light emission at the time of acquiring the second still image. When the first and third still images are acquired, the amount of white light emitted when the first to third still images are acquired It is preferable to use a value obtained from an aperture or an AE (Auto Exposure) value when the first to third still images are acquired.

In the above embodiment, four colors of light having an emission spectrum as shown in FIG. 3 are used, but the emission spectrum is not limited to this. For example, as shown in FIG. 16, the green light G and the red light R have the same spectrum as that in FIG. 3, while the violet light V ^* has a center wavelength of 410 to 420 nm and the purple light V in FIG. Light having a wavelength range slightly longer than the wavelength may be used. Further, the blue light B ^* may be light having a central wavelength of 445 to 460 nm and a wavelength range slightly shorter than the blue light B in FIG.

10, 100, 200 Endoscope system 72 Still image storage unit 74 Partial still image generation unit 76 Biological value information calculation unit 78 Light emission amount comparison unit 80 Value comparison unit

Claims (11)

A light source that emits illumination light;
An imaging unit that captures an image of the observation target illuminated with the illumination light and obtains a first still image;
A still image storage unit for storing the first still image;
A partial still image generation unit that generates a first partial still image by cutting a part of the first still image;
A display control unit that performs control to display the observation target in a moving image display area and display the first partial still image on the display unit without enlarging the observation target;
An endoscope system comprising:   The endoscope system according to claim 1, wherein the display control unit performs control to display the first partial still image in a partial still image display region different from the moving image display region.   The endoscope system according to claim 1, wherein the display control unit performs control to superimpose and display the first partial still image in the moving image display area.   The endoscope system according to claim 3, wherein an identification display for distinguishing from the moving image display is provided at an edge of the first partial still image. The imaging unit captures an image when a portion corresponding to the first partial still image enters the moving image display area, and acquires a second still image;
The still image storage unit stores the second still image,
The partial still image generation unit generates a second partial still image by cutting a part of the second still image,
5. The display control unit according to claim 1, wherein after the second still image is acquired, the display control unit performs a control to stop displaying the first partial still image and start displaying the second partial still image. The endoscope system described in the item. A biological numerical information calculation unit that calculates first biological numerical information from the first still image and calculates second biological numerical information from the second still image;
A light emission amount comparison unit that compares the light emission amount of the illumination light emitted when the first still image is acquired and the light emission amount of the illumination light emitted when the second still image is acquired;
The endoscope system according to claim 5, further comprising: a numerical correction unit that corrects at least one of the first biological numerical information or the second biological numerical information based on a comparison result of the light emission amount comparison unit. The imaging unit captures an image when a part corresponding to the second partial still image enters the moving image display area, and acquires a third still image;
The endoscope system according to claim 5 or 6, wherein the still image storage unit stores the third still image. A first imaging step in which an imaging unit captures an observation target illuminated with illumination light and obtains a first still image;
A first still image storage step in which a still image storage unit stores the first still image;
A partial still image generating unit that generates a first partial still image by cutting out a part of the first still image;
A first display control step for performing a control in which the display control unit displays the moving image of the observation target in the moving image display area and displays the first partial still image on the display unit without enlarging the display object;
A method of operating an endoscope system comprising:   The method of operating an endoscope system according to claim 8, wherein in the first display control step, control is performed to display the first partial still image in a partial still image display region different from the moving image display region.   The operation method of the endoscope system according to claim 8, wherein in the first display control step, control is performed to superimpose and display the first partial still image in the moving image display area. A second imaging step in which the imaging unit captures an image when a portion corresponding to the first partial still image enters the moving image display area to obtain a second still image;
A second still image storage step in which the still image storage unit stores the second still image;
A second partial still image generation step in which the partial still image generation unit generates a second partial still image by cutting a part of the second still image;
A second display control step for controlling the display control unit to stop displaying the first partial still image and start displaying the second partial still image after obtaining the second still image; The operation method of the endoscope system according to any one of claims 8 to 10.

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