JP5631764B2 - Endoscope system and operating method thereof - Google Patents

Description

The present invention relates to an endoscope system having a plurality of observation modes such as a normal observation mode and a special light observation mode, and an operation method thereof.

  In the medical field, many diagnoses using an endoscope are performed. Although the observation image obtained by imaging the observation site in the subject irradiated with white broadband light can observe the observation site naturally, there is a high possibility that a lesion such as a tumor will occur. It may be difficult to observe superficial blood vessels. For this reason, as described in Patent Document 1, surface blood vessels are observed by imaging the observed site while irradiating light limited to a specific narrow wavelength band (hereinafter referred to as narrow band light). An endoscope system that performs so-called special light observation that is easy to perform is known.

  In such an endoscope system, in addition to the superficial blood vessels, the entire state of the observation site is also observed at the same time, so that two types of illumination light are simultaneously emitted and two types of illumination light are simultaneously imaged. There is known a system in which narrow-band light and broadband light are mixed and simultaneously irradiated onto an observation site. This endoscope system has a plurality of observation modes in which the light amount ratios of narrowband light and broadband light are different, and an observation mode suitable for observation is selected for each type of site to be observed.

  For example, when observing the esophagus where the superficial blood vessels gather, the observation mode with an increased amount of blue narrow-band light is selected, and when observing the inside of the stomach where the dark part extends to the back, An observation mode in which the amount of light is increased is selected. As a result, the site to be observed can be observed in a suitable observation mode according to the observation conditions including the type of site to be observed. Note that the observation conditions include, for example, presence / absence of magnified observation of the observed region in addition to the type of the observed region.

JP 2009-207584 A

  By the way, since suitable observation modes may differ depending on the observation conditions, the doctor needs to memorize the types of suitable observation modes for each observation condition, and there is a problem that the burden on the doctor increases. In addition, when a suitable observation mode corresponding to the observation condition is not known and observation is performed in an observation mode other than the preferred observation mode, it is difficult to find a lesion or miss a lesion.

  The present invention has been made to solve the above problems, and an object thereof is to provide an endoscope system and a method for assisting operation thereof, in which a doctor can easily select a suitable observation mode corresponding to an observation condition. And

To achieve the above object, an endoscope system of the present invention, in the endoscope system by the endoscope to generate an observation image by imaging an object of interest in the subject, a mode for the same target site a plurality of observation modes to generate a different that seen Sazzo, the type of illumination light used to acquire the image data corresponding to each observation mode, the correspondence between the image processing performed on the light intensity and the image data storage means for storing for the type of the object of interest, and observation condition determining means for determining a viewing conditions including at least one of the type of operation to the endoscope, observation conditions are observation condition determining means has determined Correspondingly, a suitable observation mode selecting means for selecting a suitable observation mode suitable to the viewing condition from the plurality of types of observation mode, and display means for displaying a good proper observation mode, depending on the mode switching operation, suitable Comprising switch to observation mode, the type of illumination light corresponding to the switched preferred observation mode, the observation-mode switching unit Ru switched to the light amount, and image processing, the.

The display means preferably does not display an observation mode that has not been selected by the preferred observation mode selection means. Also includes a light source that selectively emits one of a plurality of types of illumination light, the endoscope is a irradiation bright light emitted from the light source, or the distal end portion of the insertion portion to be inserted into a subject irradiates the Luo object of interest, the observation mode, using the normal observation mode use of white broadband light as illumination light, the narrowband light is limited to a specific wavelength band used for the observation special light as illuminating light The special light observation mode is preferably included.

The special light observation mode, it is preferable that a plurality of modes using a least a plurality of the mixed light obtained by mixing a plurality of light at different light amount ratio comprising narrowband light as each illumination light. Additionally, mixed-light is preferably formed by mixing narrow band light and the wide band light. Furthermore, in the special light observation mode, an operation receiving unit that receives an adjustment operation of the light amount ratio, and a light amount ratio control unit that controls the light source and adjusts the light amount ratio according to the adjustment operation received by the operation receiving unit. It is preferable to provide.

The distal end of the insertion portion to be inserted into within the subject of the endoscope includes a zoom lens, a zoom mechanism for moving a's Murenzu in the optical axis direction, and an image sensor for imaging a target site through a's Murenzu is provided, the observation conditions, it is preferable to include the presence or absence of magnification observation of the object of interest that by the's Murenzu.

Storage means stores the correspondence between the observation conditions and good proper observation mode, good suitable observation mode selecting means, based on the discrimination result of the observation condition determining means, good suitable with reference to memorize means It is preferable to select an observation mode. Further, the operation for the endoscope, spraying operation for spraying the liquid at the tip or we target site of the insertion portion of the endoscope, the suction operation for sucking the fluid in及beauty destination end or we target site Is preferably included.

Against watch image data Sazzo comprises a vessel enhancement processing means for performing emphasizing vascular enhancement processing of the object of interest vessels, the type of observation modes seen by the presence or absence of execution of vascular enhancement processing is different It is preferable. Furthermore, blood vessels emphasizing processor as vascular enhancement processing, it is preferably subjected to emphasize high-pass filtering the high-frequency component with respect to images data.

Viewing means preferably displays the watch Sazzo, the synthetic composite image and a good proper observation mode. Further, the display unit preferably displays a good proper observation mode as a graphical user interface (GUI) image.

Further, the present invention, for each type of the observation mode, in the operation method of the endoscope system by endoscopes by imaging an object of interest in the subject to generate a different observation image of embodiments, the target site type If the viewing conditions including at least one of the type of operation to the endoscope, the observation condition determination step of determining by the observation condition determining means, in accordance with the observation conditions is determined by the observation condition determining step, a plurality a suitable observation mode selection step of the type of a suitable observation mode suitable to the viewing condition from the observations modes, selected by suitable observation mode selecting means, and a display step of displaying by the display means a good proper observation mode, mode In accordance with the switching operation, the observation mode switching means switches to the suitable observation mode, and switches to the type of illumination light, the amount of light, and the image processing corresponding to the switched suitable observation mode. It has a switching step to obtain, the. Moreover , it is preferable that a display step does not display the observation mode which was not selected by the suitable observation mode selection means.

  In the endoscope system and the operation assisting method thereof according to the present invention, the preferred observation mode suitable for the observation condition is selected and displayed from among the plurality of types of observation modes. Various observation modes can be easily selected.

It is a schematic diagram of an endoscope system. It is explanatory drawing for demonstrating the insertion path | route of an electronic endoscope. It is a block diagram which shows the electric constitution of an endoscope system. It is explanatory drawing for demonstrating the display of a monitor when color channel allocation is set to "normal allocation". It is explanatory drawing for demonstrating the display of a monitor when a color channel allocation is set to "special allocation." It is explanatory drawing of the GUI image which shows suitable observation mode. It is a functional block diagram of CPU. It is explanatory drawing which showed the GUI image displayed at the time of expansion observation. It is the flowchart which showed the flow of the endoscopy process. It is explanatory drawing of the monitor screen at the time of non-magnifying observation of an esophagus. It is explanatory drawing of the monitor screen at the time of magnified observation of an esophagus. It is explanatory drawing of the monitor screen at the time of non-magnifying observation of a cardia. It is explanatory drawing of the monitor screen at the time of magnified observation of a cardia. It is explanatory drawing of the monitor screen at the time of non-magnifying observation of the stomach. It is explanatory drawing of the monitor screen at the time of magnified observation of the stomach. It is a block diagram which shows the electric constitution of the endoscope system of 2nd Embodiment. It is a block diagram which shows the electric constitution of the endoscope system of 3rd Embodiment. It is a functional block diagram of CPU of 3rd Embodiment. It is explanatory drawing of the monitor screen at the time of observation of an esophagus. It is explanatory drawing of the monitor screen at the time of observation of a cardia and a stomach. It is the flowchart which showed the flow of the endoscopic inspection process of 3rd Embodiment. It is a block diagram which shows the electric constitution of the endoscope system of 4th Embodiment.

[First Embodiment]
As shown in FIG. 1, an endoscope system 10 includes an electronic endoscope 11 that images a region to be observed in a patient, and an observation image of the region to be observed based on an imaging signal obtained by the electronic endoscope 11. , A light source device 13 that emits various illumination lights for illuminating the site to be observed to the electronic endoscope 11, and a monitor 14 that displays an observation image.

  The endoscope system 10 is roughly divided into a normal observation mode for observing the entire observed region by illuminating the inside of the body with a broadband light such as white light, and an observed region with a narrow band light whose wavelength band is limited. And a special light observation mode for observing in a state where blood vessels and the like are highlighted.

  In the special light observation mode, “BLI-M1 mode (hereinafter simply referred to as M1 mode)”, “BLI-E mode (hereinafter simply referred to as E mode), and the like, which differ in the amount of narrowband light and the presence or absence of image processing, There are four types of modes: “BLI-M2 mode (hereinafter simply referred to as M2 mode)” and “BLI-M3 mode (hereinafter simply referred to as M3 mode)”.

  The electronic endoscope 11 is connected to a flexible insertion portion 16 to be inserted into the body and a proximal end portion of the insertion portion 16, and is used for gripping the electronic endoscope 11 and operating the insertion portion 16. And a universal cord 18 for connecting the operation unit 17 to the processor device 12 and the light source device 13, respectively.

  The insertion portion distal end portion 16a that is the distal end portion of the insertion portion 16 incorporates an optical system, an image sensor, and the like that are used for illuminating and photographing the observed portion. In addition to the observation window 19 (see FIG. 3) and the illumination window 20 (see FIG. 3), an air / water supply nozzle, which is not shown, is inserted into the distal end surface of the insertion portion distal end portion 16a. A forceps outlet or the like serving as an outlet of the forceps channel is provided. A bendable bending portion 16b is connected to the rear end of the insertion portion distal end portion 16a.

  The operation unit 17 is provided with an angle knob 21, an operation button 22, a forceps inlet 23, and the like. The angle knob 21 is rotated when adjusting the bending direction and the bending amount of the insertion portion 16. The operation button 22 is used for various operations such as air / water supply and suction. The forceps inlet 23 communicates with the forceps channel.

  The universal cord 18 incorporates an air / water channel, a signal cable, a light guide, and the like. A connector portion 25 a is provided at the distal end portion of the universal cord 18. This connector portion 25 a is connected to the light source device 13. Further, the connector part 25b branches from the connector part 25a. This connector portion 25 b is connected to the processor device 12.

  As shown in FIG. 2, the electronic endoscope 11 is a so-called upper digestive tract endoscope in which the insertion portion 16 is inserted into the body from the mouth of the patient H, and the esophagus E, cardia as indicated by arrows in the figure. The inside of each upper digestive tract such as C and stomach S is photographed in order.

  As shown in FIG. 3, the light source device 13 includes a broadband light source 30, a blue semiconductor laser device (hereinafter simply referred to as blue LD) 31, a light combining unit 32, and movable apertures (hereinafter simply referred to as apertures) 34a and 34b. A condensing lens 35 and a light source drive unit 37.

  As the broadband light source 30, for example, a xenon lamp, a white LED, or a micro white light source (a set of a light source that emits light having a central wavelength of 445 nm and a phosphor that emits excitation light by irradiation of this light) is used. To WB in the blue region (about 470 to 700 nm). The broadband light source 30 always emits broadband light BB. The broadband light BB enters the light combining unit 32 directly or through an optical fiber (not shown).

  The blue LD 31 emits blue (B) narrow band light Bn limited to a specific wavelength band of blue (for example, a center wavelength of 405 nm) in the special light observation mode. In addition, you may use LED etc. instead of LD as a light source of B narrow-band light Bn. Similarly to the broadband light BB, the B narrowband light Bn also enters the light combining unit 32 directly or via an optical fiber (not shown).

  The wavelength band of the B narrowband light Bn is adjusted in accordance with, for example, the absorption peak (near 415 nm) of the absorption spectrum of hemoglobin light. From the knowledge about the light scattering characteristics of the living tissue, most of the irradiated light is absorbed by the surface blood vessel and does not return to the insertion portion tip 16a unless the wavelength of the irradiated light exceeds about 470 nm. On the contrary, in the living tissue around the superficial blood vessel, most of the irradiated light is reflected by the relatively strong scattering characteristics and returns to the insertion portion distal end portion 16a. As a result, the contrast between the superficial blood vessel and the surrounding biological tissue becomes extremely high, so that the superficial blood vessel can be sufficiently highlighted.

  On the other hand, highlighting of the middle-deep blood vessels is performed using green light having a wavelength included in the broadband light BB of approximately 500 nm to 600 nm. From the knowledge about the light scattering characteristics of living tissue, when the wavelength of the irradiated light is between 500 nm and 600 nm, the light reaches the mid-deep blood vessel deeper than the surface blood vessel. While this light is absorbed by the middle-deep blood vessel, it is reflected and scattered by the living tissue around the middle-deep blood vessel. As a result, the contrast between the mid-deep blood vessel and the surrounding biological tissue is increased, so that the mid-deep blood vessel and the like can be sufficiently highlighted. Note that the broadband light BB includes light other than green light, but the wavelength band in which the middle-layer blood vessel can be highlighted is sufficiently wider than the wavelength band in which the surface blood vessel can be highlighted. For this reason, the contrast reduction of the middle-deep blood vessel due to the influence of light other than green light can be minimized.

  The light combining unit 32 is, for example, a dichroic mirror or an optical coupler, and mixes the broadband light BB and the B narrowband light Bn and emits them toward the condenser lens 35.

  The diaphragm 34 a is disposed in front of the broadband light source 30 and adjusts the amount of broadband light BB emitted from the broadband light source 30. The stop 34b is disposed in front of the blue LD 31 and adjusts the amount of B narrowband light Bn emitted from the blue LD 31. The condenser lens 35 causes the broadband light BB and the B narrowband light Bn incident from the light combining unit 32 to enter the light guide 41.

  The light source driving unit 37 controls ON (lit) / OFF (dark) of the blue LD 31 under the control of the processor device 12. The light source driving unit 37 turns off the blue LD 31 in the normal observation mode and turns on the blue LD 31 in the special light observation mode.

  Further, the light source driving unit 37 changes the area of the apertures of the apertures 34a and 34b under the control of the processor device 12, so that the broadband light emitted from the broadband light source 30 and the blue LD 31 in each mode of the special light observation mode. The light amount ratio between the light BB and the B narrowband light Bn is controlled. In the M1 mode, the light source driving unit 37 stops the light amount of the broadband light BB so that the light amount of the B narrowband light Bn is larger than the light amount of the B narrowband light Bn in the E mode. 34a and 34b are controlled. In addition, the light source driving unit 37 controls the diaphragms 34a and 34b in the M2 mode and the M3 mode so that the ratio of the light amount of the broadband light BB is higher than that in the M1 mode. In the M2 to M3 modes, the light amount ratio is set to the same value.

  With each configuration described above, the light source device 13 causes the broadband light BB to enter the light guide 41 in the normal observation mode, and the broadband light BB and the B narrow band having different light quantity ratios in the M1 mode, E mode, and M2 to M3 modes, respectively. The mixed light with the light Bn is incident on the light guide 41.

  The electronic endoscope 11 includes a light guide 41, a zoom lens 42, a zoom mechanism 43, a CCD image sensor (hereinafter referred to as a CCD) 44 corresponding to the image pickup means of the present invention, and an analog processing circuit (AFE: Analog Front End) 45. The imaging control unit 46 is provided. The light guide 41 is a large-diameter optical fiber, a bundle fiber, or the like. The light guide 41 has an incident end inserted into the light source device 13 and an emission end opposed to the irradiation lens 48 provided in the insertion portion distal end portion 16a. The illumination light incident on the irradiation lens 48 from the light guide 41 is irradiated to the observation site through the illumination window 20. Then, the light reflected / scattered at the site to be observed enters the condenser lens 51 through the observation window 19.

  The zoom lens 42 is disposed between the condenser lens 51 and the CCD 44 so as to be movable in the direction of the optical axis O. The zoom mechanism 43 performs zooming by moving the zoom lens 42 in the optical axis direction under the control of the processor device 12.

  The CCD 44 has an imaging surface in which a plurality of photodiodes 52 (hereinafter referred to as PD 52, see FIG. 4) are two-dimensionally arranged, and subject light incident through the condenser lens 51 and the zoom lens 42 is electrically transmitted by each PD 52. Converted into a typical image signal and output to the AFE 45. A MOS type image sensor may be used instead of the CCD. An imaging control unit 46 controlled by the processor device 12 is connected to the CCD 44. The CCD 44 outputs an imaging signal to the AFE 45 at a predetermined frame rate based on the drive signal from the imaging control unit 46.

  As shown in FIG. 4, the CCD 44 is a color CCD including red, green, and blue microfilters FR, FG, and FB two-dimensionally arranged on each PD 52. The CCD 44 includes an R pixel composed of a microfilter FR and a PD 52 disposed below (in the drawing, side, the same applies hereinafter), a G pixel composed of a microfilter FG and a PD 52 disposed below, and a microfilter FB. And a B pixel composed of PD 52 disposed below the B pixel.

  The microfilter FR transmits red (R) light in the red band. The microfilter FG transmits green (G) light in the green band. The microfilter FB transmits blue (B) light in the blue band. The light incident on the imaging surface 44a can be separated into three colors of RGB by the microfilters FR, FG, and FB. The B light includes B narrowband light Bn.

  Returning to FIG. 3, although not shown, the AFE 45 includes a correlated double sampling circuit (CDS), an automatic gain control circuit (AGC), and an analog / digital converter (A / D). The CDS performs correlated double sampling processing on the imaging signal from the CCD 44 to remove noise. The AGC amplifies the imaging signal from which noise has been removed by CDS. The A / D converts the image pickup signal amplified by the AGC into a digital image pickup signal having a predetermined number of bits and sends it to the processor device 12.

  The processor device 12 includes a memory (storage means) 53, a CPU 54, a digital signal processor (DSP) 55, a frame memory 56, a display control circuit 58, a mode switch 59, and a zoom switch 60. And. The memory 53 stores various programs and data for controlling the endoscope system 10.

  The CPU 54 is connected to each unit of the processor device 12 and the light source driving unit 37 of the light source device 13 through signal lines, and comprehensively controls them based on programs and data read from the memory 53.

  The DSP 55 performs signal processing such as white balance adjustment, color tone processing, gradation processing, and sharpness processing on the imaging signal input from the AFE 45. In the normal observation mode, the DSP 55 performs the above signal processing on the B imaging signal, the G imaging signal, and the R imaging signal input from the AFE 45, thereby generating normal image data having pixel values of three colors B, G, and R. Generate. The normal image data is stored in the frame memory 56.

  On the other hand, in each special light observation mode, the DSP 55 performs appropriate signal processing on the B imaging signal (including the B narrowband imaging signal), the G imaging signal, and the R imaging signal input from the AFE 45, so that B, Special light image data having pixel values of three colors G and R is generated. This special light image data is also stored in the frame memory 56.

  When the observation mode is the normal observation mode, the display control circuit 58 reads the normal image data from the frame memory 56 and displays the observation image on the monitor 14 based on the normal image data. At this time, as shown in FIG. 4, the pixel values of the three colors B, G, and R of the normal image data are assigned to the B channel, G channel, and R channel of the monitor 14 and output. Further, even when the observation mode is the M2 to M3 mode, the display control circuit 58 converts the B, G, and R pixel values of the special light image data into the B channel, G channel, and R of the monitor 14, respectively. Assign to a channel and output.

  On the other hand, as shown in FIG. 5, when the observation mode is the M1 to E mode, the display control circuit 58 reads the special light image data from the frame memory 56 and observes it on the monitor 14 based on the special light image data. Display the image. At this time, the B pixel value acquired by the B pixel of the CCD 44 is assigned to the B and G channels of the monitor 14, and the G pixel value acquired by the G pixel is assigned to the R channel of the monitor 14. The surface blood vessel portion of the observation image displayed on the monitor 14 is displayed in brown because the B and G channels become darker and only the R channel becomes relatively brighter due to the absorption of the B narrowband light Bn. In addition, since the R channel becomes dark due to absorption of G light having a wavelength of about 500 nm to 600 nm, the middle-deep blood vessel portion is displayed in a cyan color or green color in which the B and G channels are mixed.

  The display control circuit 58 is provided with a graphical user interface (GUI) display unit 58a. As shown in FIG. 6, the GUI display unit 58a generates a GUI image 62 indicating an observation mode suitable for observation under the current observation conditions (hereinafter referred to as a preferred observation mode) under the control of the CPU 54. The GUI image 62 is combined with the observation image and displayed on the monitor 14. Reference numeral 63 denotes a cursor for selecting the GUI image 62.

  Returning to FIG. 3, the mode switch 59 is provided, for example, on the front panel of the processor device 12 and is operated when switching the observation mode. When the cursor 63 is moved by operating the mode switch 59 to select the GUI image 62, switching to the observation mode corresponding to the GUI image 62 selected by the cursor 63 is confirmed. The CPU 54 controls each part of the processor device 12 and the light source device 13 according to the type of the observation mode selected by the mode changeover switch 59 to change the illumination light and display the observation image displayed on the monitor 14. Perform switching, etc.

  The zoom switch 60 is, for example, a foot pedal type switch connected to the processor device 12 and is operated when zooming at the time of shooting is changed. The CPU 54 moves the zoom lens 42 by controlling the zoom mechanism 43 in accordance with the zooming operation performed by the zoom switch 60. Thus, the zoom magnification is set to a doctor's desired magnification. A zoom switch may be provided on the operation unit 17 of the electronic endoscope 11.

  As shown in FIG. 7, in addition to the above-described programs and data, the memory 53 includes an observation mode selection table (hereinafter simply referred to as a selection table) 65 and an observation mode execution table (hereinafter simply referred to as an execution table). 66) is stored.

  In the selection table 65, the type of the site to be observed, the observation conditions including the non-magnification observation / magnification observation of the site to be observed, and the preferred observation mode under each observation condition are stored in association with each other. The preferred observation mode is an observation mode in which “◯” is registered in each observation mode.

  The normal observation mode and the M1 to E modes are selected as preferred observation modes under all observation conditions. The M2 to M3 modes are selected as a preferred observation mode during non-magnification observation regardless of the type of the observation site because the ratio of the light amount of the broadband light BB is set high. By referring to the selection table 65, a suitable observation mode can be selected for each observation condition.

  In the execution table 66, each observation mode, the light quantity ratio between the broadband light BB and the B narrowband light Bn under each observation mode, and color channel assignment indicating assignment of each color pixel value to each color channel of the monitor 14 are displayed. And whether or not high-pass filter (HPF) processing is performed on the image data stored in the frame memory 56 is stored in association with each other.

  The light amount ratio (BB: Bn) is 100: 0 in the normal observation mode because the blue LD 31 is turned off. In the other M1, E, M2, and M3 modes, the light quantity ratios are set to “2: 1”, “1: 4”, “3: 1”, and “3: 1”, respectively.

  There are two types of color channel allocation: normal allocation and special allocation. In the normal allocation, the pixel values of the three colors B, G, and R of the image data are output to the B channel, G channel, and R channel of the monitor 14, respectively. In the special allocation, the B pixel value of the image data is output to the B and G channels, and the G pixel value is output to the R channel.

  The execution of the HPF process is set in the E, M1-M2 mode. Therefore, the difference between the M2 mode and the M3 mode is the presence or absence of HPF processing. By referring to such an execution table 66, it is possible to determine the light amount ratio, color channel assignment, and presence / absence of HPF processing from the type of observation mode.

  The CPU 54 sequentially executes various programs read from the ROM, so that the observation condition determination unit 69, the preferred observation mode selection unit 70, the light source control unit 71, the display control unit 72, and the HPF processing unit (blood vessel enhancement processing means) 73 are obtained. Function. The display control unit 72 constitutes the display means of the present invention together with the monitor 14.

  The observation condition discriminating unit 69 discriminates the observation conditions including the type of the site to be observed and the presence or absence of magnified observation of the site to be observed. The type of site to be observed (esophagus E, cardia C, stomach S) is determined by analyzing image data newly stored in the frame memory 56. For example, the diameter of the upper gastrointestinal tract from the esophagus E to the stomach S is not constant but is different in each part. Specifically, the upper gastrointestinal tract has the smallest cardia C, and the stomach S has the largest diameter. In the image data, the internal space of the upper gastrointestinal tract located in the forward direction of the insertion portion distal end portion 16a is a dark portion BL (see FIG. 10). For this reason, the kind of to-be-observed site | part can be discriminate | determined by calculating | requiring the area of the dark part BL.

  For example, when the area of the dark part BL is not less than a predetermined area lower limit value and less than the area upper limit value, it is determined that the site to be observed is the esophagus E. Further, when the area of the dark part BL is less than the area lower limit value, it is determined that the site to be observed is the cardia C. When the area of the dark part BL is equal to or larger than the area upper limit value, it is determined that the site to be observed is the stomach S. Since the area of the dark portion BL changes even when the zoom magnification is changed, each upper limit value and each lower limit value are determined for each zoom magnification.

  The presence / absence of magnified observation of the part to be observed is determined based on the result of detecting the zoom magnification based on information such as the position of the zoom lens 42, for example. Specifically, when the zoom magnification exceeds a predetermined magnification upper limit value, magnified observation is performed, and when the zoom magnification is equal to or smaller than the magnification upper limit value, it is determined that non-magnification observation is performed. The discrimination result of the observation condition including the type of the site to be observed and the presence / absence of magnified observation is sequentially input to the preferred observation mode selection unit 70.

  The suitable observation mode selection unit 70 refers to the selection table 65 based on the determination result of the observation condition determination unit 69 and selects a suitable observation mode from among the observation modes. The selection result of the preferred observation mode is sequentially input to the display control unit 72.

  The light source control unit 71 refers to the execution table 66 and controls the light source driving unit 37 according to the observation mode selected by the mode switch 59 to turn on / off the blue LD 31 and the broadband light BB. The light amount ratio of the B narrow band light Bn is controlled.

  The display control unit 72 refers to the execution table 66, determines the color channel assignment corresponding to the observation mode selected by the mode switch 59, and controls the display control circuit 58 according to this determination. Thereby, the color tone of the observation image displayed on the monitor 14 changes according to the kind of site to be observed.

  Further, the display control unit 72 controls the GUI display unit 58 a so that the GUI image 62 indicating the preferred observation mode selected by the preferred observation mode selection unit 70 is displayed on the monitor 14. As shown in FIG. 6, GUI images 62 corresponding to all the observation modes are combined and displayed on the observation image at the time of non-magnification observation regardless of the type of the observation site. On the other hand, as shown in FIG. 8, only the GUI image 62 showing the normal observation mode, the M1 mode, and the E mode is displayed at the time of the enlarged observation regardless of the type of the observation site, and as shown by the dotted lines in FIG. The GUI image 62 indicating the M3 mode is not displayed.

  Returning to FIG. 7, the HPF processing unit 73 emphasizes the high frequency components of the image data stored in the frame memory 56 under the observation mode in which the HPF processing is set to ON in the execution table 66. Perform HPF treatment. The HPF process is a kind of spatial frequency processing, and emphasizes the edge of the surface blood vessel at the site to be observed. Thereby, the superficial blood vessels in the observation image are more highlighted. Since the HPF processing method is well known, a detailed description thereof is omitted here.

  Next, the operation of the endoscope system 10 having the above configuration will be described using the flowchart shown in FIG. When the power of the processor device 12 and the light source device 13 is turned on and the preparation process for the endoscopic examination is performed, the driving of the CCD 44 is started and the broadband light source BB is emitted from the broadband light source 30. In the initial state when the power is turned on, the observation mode is set to the normal observation mode, and the zoom magnification is set to 1. When the preparation for examination is completed, the insertion portion 16 is inserted into the esophagus E from the mouth of the patient H.

[Oesophageal observation]
The broadband light BB emitted from the broadband light source 30 enters the light guide 41 through the light combining unit 32 and the condenser lens 35, and is further irradiated into the esophagus E through the light guide 41, the illumination window 20, and the like. Thereby, the broadband light BB reflected / scattered in the esophagus E enters the observation window 19 and further enters the CCD 44 through the condenser lens 51 and the zoom lens 42. As shown in FIG. 4, the broadband light BB incident on the CCD 44 is separated into three colors by the microfilters FR, FG, and FB and received by the PD 52.

  Each PD 52 converts the received light into an electrical imaging signal and outputs it to the AFE 45. The AFE 45 performs various kinds of signal processing on the imaging signal from the CCD 44 and outputs digital blue imaging signals, green imaging signals, and red imaging signals to the DSP 55 of the processor device 12. Each color imaging signal is subjected to various signal processing by the DSP 55 and then stored in the frame memory 56 as normal image data.

  The observation condition discriminating unit 69 discriminates the type of the site to be observed based on the area of the dark part BL (see FIG. 10) obtained by analyzing the normal image data newly stored in the frame memory 56. In addition, the observation condition determination unit 69 determines whether non-magnification observation or magnification observation is performed based on the zoom magnification obtained by detecting information such as the position of the zoom lens 42. In this case, it is determined that the esophagus E is not magnified as an observation condition, and the determination result is input to the preferred observation mode selection unit 70.

  The suitable observation mode selection unit 70 refers to the selection table 65 based on the determination result input from the observation condition determination unit 69 and selects a suitable observation mode from among the observation modes. In this case, all observation modes are selected as preferred observation modes. Then, the suitable observation mode selection unit 70 sends the selection result of the suitable observation mode to the display control unit 72.

  The display control unit 72 refers to the execution table 66, determines normal allocation as color channel allocation corresponding to the normal observation mode, and issues a normal allocation display command to the display control circuit 58. The display control unit 72 issues a GUI image display command including the selection result of the preferred observation mode input from the preferred observation mode selection unit 70 to the GUI display unit 58a. Since the HPF processing is not performed in the normal observation mode, the HPF processing unit 73 is in a standby state.

  The display control circuit 58 receives the normal allocation display command from the display control unit 72, reads the normal image data newly stored in the frame memory 56, and the three-color pixels B, G, and R of this normal image data The values are output to the B, G, and R channels of the monitor 14, respectively. Thereby, the observation image 76a of the esophagus E is displayed on the monitor 14 as shown in FIG. In addition, the code | symbol V1 in a figure is a surface layer blood vessel.

  In addition, the GUI display unit 58a receives a GUI image display command from the display control unit 72, synthesizes the GUI image 62 indicating each of all the observation modes selected as the preferred observation mode with the observation image 76a, and displays it on the monitor 14. Let Based on the GUI image 62 displayed on the monitor 14, the doctor can easily determine a suitable observation mode suitable for the current observation condition (non-enlarged observation of the esophagus E). Thereafter, the above-described processing is repeatedly executed until the observation condition and the observation mode are changed.

  As a result of observing the observation image 76a, when more detailed observation is performed such as when an abnormality is found in the esophagus E, the zoom switch 60 is operated to increase the zoom magnification. In response to this operation, the CPU 54 controls the zoom mechanism 43 to move the zoom lens 42 to increase the zoom magnification. As a result, an enlarged observation image 76b (see FIG. 11) in which the inside of the esophagus E is enlarged is displayed on the monitor 14.

  At this time, when the zoom magnification exceeds the magnification upper limit value, the observation condition determination unit 69 determines that the observation condition is switched from non-magnification observation to magnification observation. Then, the observation condition determination unit 69 sends a new observation condition determination result to the preferred observation mode selection unit 70.

  The suitable observation mode selection unit 70 refers to the selection table 65 based on the determination result from the observation condition determination unit 69 and selects the normal observation mode, the M1 mode, and the E mode as the preferable observation mode, and the selection result. Is input to the display control unit 72. The display control unit 72 issues a normal allocation display command to the display control circuit 58 in the same way as during non-magnifying observation, and also issues a GUI image display command including a selection result of a new preferred observation mode to the GUI display unit 58a. To emit.

  As shown in FIG. 11, the display control circuit 58 receives the normal assignment display command from the display control unit 72, reads the normal image data newly stored in the frame memory 56, and reads the normal image data in the esophagus E to the monitor 14. The enlarged observation image 76b is displayed.

  At the same time, the GUI display unit 58a receives a GUI image display command from the display control unit 72, combines the GUI image 62 indicating each of the three observation modes selected as the preferred observation mode with the enlarged observation image 76b, and monitors it. 14 is displayed. Thus, the doctor can easily determine that the three observation modes are the preferred observation modes in the enlarged observation of the esophagus E. In addition, since the GUI image 62 indicating the M2 to M3 mode suitable for non-magnifying observation is not displayed on the monitor 14, it is possible to prevent the observation mode from being erroneously switched to the M2 to M3 mode.

  Hereinafter, until the observation condition and the observation mode are changed, the acquisition of the normal image data, the determination of the observation condition, the selection of the suitable observation mode, and the display of the enlarged observation image 76b and the GUI image 62 are continued. When the zoom switch 60 is operated to decrease the zoom magnification and the observation condition returns to “non-enlarged observation of the esophagus”, the display of the observation image 76a and the GUI image 62 shown in FIG. Executed.

  In order to highlight the surface blood vessels in the observation image 76a or the enlarged observation image 76b, the mode selector switch 59 is switched to, for example, the E mode. In response to this switching operation, the light source control unit 71 refers to the execution table 66 to determine the operation of the blue LD 31 and the light amount ratio between the broadband light BB and the B narrowband light Bn. Then, the light source control unit 71 issues a special light irradiation command including information on the light amount ratio (BB: Bn = 1: 4) to the light source driving unit 37.

  The light source driving unit 37 receives the special light irradiation command from the light source control unit 71, turns on the blue LD 31, and controls the diaphragms 34a and 34b to transmit the broadband light BB and B narrow light from the broadband light source 30 and the blue LD 31, respectively. The band light Bn is emitted with a light amount ratio of 1: 4. The B narrowband light Bn emitted from the blue LD 31 is mixed with the broadband light BB in the light combining unit 32. The mixed light BB, Bn of the broadband light BB and the B narrowband light Bn is irradiated into the esophagus E through the light guide 41 and the like.

  The mixed light BB, Bn reflected / scattered in the esophagus E enters the CCD 44 through the observation window 19 and the like, is color-separated by the microfilters FR, FG, FB, and is received by the PD 52, respectively. Each PD 52 converts each received light into an electrical imaging signal and outputs it to the AFE 45. As a result, each color imaging signal is sent from the AFE 45 to the DSP 55, and the special light image data is generated by the DSP 55 and stored in the frame memory 56.

  After storing the special light image data, as in the normal observation mode, the determination of the observation condition and the selection of the preferred observation mode are executed. The HPF processing unit 73 refers to the execution table 66 and performs HPF processing on the special light image data stored in the frame memory 56 when the observation mode is the E mode.

  Next, the display control unit 72 refers to the execution table 66, determines the special assignment as the color channel assignment corresponding to the E mode, and issues a special assignment display command to the display control circuit 58. The display control unit 72 issues a GUI image display command for all observation modes to the GUI display unit 58a when the observation condition is non-magnification observation, and conversely, when the observation condition is magnification observation, A GUI image display command for the M1 mode and the E mode is issued to the GUI display unit 58a.

  Upon receiving the special assignment display command from the display control unit 72, the display control circuit 58 reads the special light image data newly stored in the frame memory 56, and sets the B pixel value of the special light image data as B, B of the monitor 14. In addition to outputting to the G channel, the G pixel value is output to the R channel of the monitor 14. Thereby, the observation image 76a or the enlarged observation image 76b in the esophagus E under the illumination light including the B narrow band light Bn is displayed. The display of the GUI image 62 is the same as that in the normal observation mode shown in FIGS.

  In the E mode, since the amount of the B narrowband light Bn is increased, the B narrowband imaging signal is amplified. The special light image data is subjected to HPF processing for enhancing the edge of the surface blood vessel. As a result, the superficial blood vessels gathered in the esophagus E are more highlighted in the observation image 76a or the enlarged observation image 76b. Thereby, the superficial blood vessels can be observed intensively.

  On the other hand, even when the observation mode is switched to the M1 to M3 mode (when the M2 to M3 mode is in non-magnification observation), the basic processing is performed except that the light amount ratio, the color channel assignment, and the presence or absence of the HPF processing are different. Is the same as the normal observation mode and the E mode. Therefore, the GUI image 62 shown in FIG. 10 is synthesized and displayed in the observation image during non-magnification observation, and the GUI image 62 shown in FIG. 11 is synthesized and displayed in the magnification observation image during magnification observation.

[Observation of Cardia]
After observing the esophagus E, the observation mode is switched to the normal observation mode, and the zoom magnification is returned to 1. Next, the insertion portion distal end portion 16a is pushed further into the esophagus E. When the insertion portion distal end portion 16a reaches the vicinity of the cardia C, the area of the dark portion BL in the observation image 76a rapidly decreases. The observation condition discriminating unit 57 discriminates that the site to be observed is the cardia C when the area of the dark part BL is less than a predetermined area lower limit value, and discriminates the observation condition indicating “non-magnifying observation of the cardia” The result is sent to the preferred observation mode selection unit 70.

  The preferred observation mode selection unit 70 receives the determination result from the preferred observation mode selection unit 70 and selects the preferred observation mode with reference to the selection table 65. Thereafter, similarly to the “non-enlarged observation of the esophagus”, as shown in FIG. 12, the observation image 77a of the cardia C and the GUI image 62 are displayed on the monitor 14. At this time, the preferred observation mode at the time of “non-magnification observation of the cardia” is the same as that at the time of “non-magnification observation of the esophagus”, so that the GUI image 62 indicating each of all the observation modes is displayed on the monitor 14. In addition, the code | symbol V2 in a figure is a middle-deep layer blood vessel.

  When performing detailed observation of the cardia C and its surrounding area, the zoom switch 60 is used to increase the zoom magnification. Thereby, as shown in FIG. 13, the enlarged observation image 77b which expanded the cardia C and its peripheral site | part is displayed. At this time, since the preferred observation mode at the time of “magnification observation of the cardia” is the same as that at the time of “magnification observation of the esophagus”, the GUI image 62 indicating the normal observation mode, the M1 mode, and the E mode is displayed in the enlarged observation image 77b. Composite display.

  When the observation mode is switched to a mode other than the normal observation mode, the basic process is the same as the normal observation mode except that the light amount ratio and the presence or absence of the HPF process are different. Description is omitted.

  In addition, middle-deep blood vessels are gathered around the cardia C. For this reason, the light quantity of the broadband light BB irradiated to the peripheral part of the cardia C increases by selecting M1-M3 mode as an observation mode. As a result, the amount of G light with a wavelength of around 500 nm to 600 nm irradiated to the peripheral part of the cardia C also increases. Thereby, since the middle-deep blood vessel is highlighted, the middle-deep blood vessel can be intensively observed. In addition, since the light amount of the broadband light BB increases, it becomes easy to grasp the entire state of the observed site.

[Observation of stomach]
After the cardia C is observed, the observation mode is set to the normal observation mode, and the zoom magnification is returned to 1. Next, the insertion portion distal end portion 16a is pushed further into the cardia C. When the insertion portion distal end portion 16a reaches the inside of the stomach S, the area of the dark portion BL in the observation image 77a increases rapidly. The observation condition discriminating unit 57 discriminates that the site to be observed is the stomach S when the area of the dark part BL is equal to or larger than the predetermined area upper limit value, and discriminates the observation condition indicating “non-magnifying observation of the stomach” The result is sent to the preferred observation mode selection unit 70.

  The preferred observation mode selection unit 70 receives the determination result from the preferred observation mode selection unit 70 and selects the preferred observation mode with reference to the selection table 65. Thereafter, similarly to the “non-enlarged observation of the esophagus and cardia”, the observation image 78a and the GUI image 62 in the stomach S are displayed on the monitor 14, as shown in FIG.

  Further, when performing detailed observation in the stomach S, the zoom switch 60 is operated to increase the zoom magnification. As a result, as shown in FIG. 15, an enlarged observation image 78 b in which the stomach S is enlarged is displayed on the monitor 14. At this time, since the preferred observation mode at the time of “magnification observation of the stomach” is the same as that at the time of “magnification observation of the esophagus”, the GUI image 62 indicating the normal observation mode, the M1 mode, and the E mode is enlarged. The combined display is displayed at 78b.

  As in the case of observation of the esophagus E and cardia C, when the observation mode is switched from the normal observation mode to another mode, the basic process is the same except that the light amount ratio and the presence or absence of the HPF process are different. Since it is the same as the normal observation mode, a specific description is omitted here.

  Similarly, when removing the insertion portion 16 from the body of the patient H, similarly, determination of observation conditions, acquisition of image data, selection of a suitable observation mode, and execution of HPF processing in the M1 to M2 and E modes The observation image and the GUI image are continuously displayed.

  Since the GUI image 62 indicating the preferred observation mode corresponding to the observation condition is displayed on the monitor 14, the doctor need not store the type of the preferred observation mode for each observation condition, and the burden on the doctor can be reduced. Further, switching to an observation mode other than the preferred observation mode is prevented. As a result, it is prevented that the lesion is difficult to find, and the possibility of missing the lesion is further reduced. In addition, even though a large number of observation modes are prepared, they are not used and the observation modes can be effectively used.

[Second Embodiment]
Next, an endoscope system 80 according to the second embodiment of the present invention will be described with reference to FIG. In the first embodiment, the light amount ratio between the broadband light BB and the B narrow band light Bn in each special light observation mode is fixed. However, in the endoscope system 80, the light amount ratio can be adjusted. Yes.

  The endoscope system 80 has the same configuration as that of the endoscope system 10 of the first embodiment except that a processor device 81 different from that of the first embodiment is provided. The same components are denoted by the same reference numerals, and the description thereof is omitted.

  In the processor device 81, except that the execution table 82 is stored in the memory 53, the light amount ratio changeover switch 83 is connected to the CPU 54, and the CPU 54 functions as a light source control unit (light amount ratio control means) 84. The configuration is basically the same as that of the processor device 12 of the first embodiment.

  The execution table 82 is basically the same as the execution table 66 of the first embodiment, but the adjustment amount of the light amount ratio between the broadband light BB and the B narrowband light Bn in each mode of the special light observation mode is different. It has been established. For example, in the E mode, the light amount ratio can be changed within an adjustment range of “0.5: 3.5” to “0.5: 4.5”.

  The light quantity ratio switch 83 is, for example, a foot pedal type switch, and is pressed when changing the light quantity ratio in the special light observation mode. The light source control unit 84 is basically the same as the light source control unit 71 of the first embodiment. However, the light source control unit 84 sets the apertures 34a and 34b so that the light amount ratio changes stepwise within the adjustment range set in the execution table 82 every time the light amount ratio switch 83 is pressed. The amount of light of the broadband light BB and B narrowband light Bn is adjusted by control.

  The method for adjusting the light amount ratio is not particularly limited, and the light amount of one of the broadband light BB and the B narrow band light Bn is increased or decreased according to the pressing operation of the light amount ratio changeover switch 83, and the broadband light BB and the B narrow band are increased. Various adjustment methods may be used such as increasing or decreasing both the light amounts of the light Bn, or increasing the light amount of one of the broadband light BB and the B narrowband light Bn and decreasing the other light amount.

  In the second embodiment, the foot pedal has been described as an example of the light quantity ratio switch 83, but the light quantity ratio switch 83 is provided on the operation panel of the processor device 81 or the operation unit 17 of the electronic endoscope 11. It may be provided.

[Third Embodiment]
Next, an endoscope system 87 according to a third embodiment of the present invention will be described with reference to FIG. The endoscope system 10 according to the first embodiment has the E, M1 to M3 modes for performing blood vessel highlighting as the special light observation mode. However, the endoscope system 87 is added to the above modes. It has an AFI (Auto Fluorescence Imaging) mode and a low O ₂ mode.

  The AFI mode is a mode for performing autofluorescence observation of the site to be observed. In the AFI mode, autofluorescence having a wavelength of 500 nm to 630 nm observed when the observation site is irradiated with excitation light having a wavelength of 390 nm to 470 nm is detected, imaged, and displayed on the monitor 14.

In the low O ₂ mode, information on the oxygen saturation of hemoglobin in the blood vessel is obtained by utilizing the difference in light absorption characteristics between oxyhemoglobin and deoxyhemoglobin, and the light penetration depth varies depending on the wavelength band. This mode is for obtaining depth information. In the low O ₂ mode, for example, both the oxygen saturation and the blood vessel depth are based on the luminance ratio between the imaging signals obtained by irradiating the site to be observed with three narrowband lights having center wavelengths of 405 nm, 445 nm, and 473 nm. Is obtained, imaged, and displayed on the monitor 14.

  The endoscope system 87 includes a light source device 88, an electronic endoscope 89, and a processor device 90. In addition, the same code | symbol is attached | subjected about the same thing as the said 1st Embodiment and a structure, and the description is abbreviate | omitted.

The light source device 88 has basically the same configuration as that of the light source device 13 of the first embodiment, except that the first to fourth blue LDs 92 to 95, the diaphragm 96, and the light source driving unit 97 are provided. The first blue LD 92 corresponds to the blue LD 31 of the first embodiment, and emits B narrowband light Bn1 having a center wavelength of 405 nm in the E, M1 to M3 and low O ₂ modes. In addition, a stop 34b is arranged in front of the first blue LD 92 as in the first embodiment.

The second to third blue LDs 93 and 94 emit B narrow band lights Bn2 and Bn3 having center wavelengths of 445 nm and 473 nm, respectively, in the low O ₂ mode. The fourth blue LD 95 emits blue (B) excitation light Bn4 having a wavelength of 390 nm to 470 nm in the AFI mode.

The diaphragm 96 is disposed in front of the fourth blue LD 95, and adjusts the amount of B excitation light Bn4 emitted from the fourth blue LD 95. Note that, in the low O ₂ mode, the light amount ratio is not adjusted, so that a diaphragm is not disposed in front of the second to third blue LDs 93 and 94.

The light source driver 97 controls ON / OFF of the broadband light source 30 and the first to fourth blue LDs 92 to 95 under the control of the processor device 90. The light source driver 97 turns off the broadband light source 30 in the low O ₂ mode and turns on the broadband light source 30 in other modes.

The light source driver 97 turns off the first blue LDs 92 to 95 in the normal observation mode, turns on the first blue LD 92 in the E and M1 to M3 modes, and turns on the fourth blue LD 95 in the AFI mode. To do. The light source driving unit 97 switches ON / OFF of the first to third blue LDs 92 to 94 so that the B narrowband lights Bn1 to Bn3 are emitted sequentially and repeatedly in the low O ₂ mode.

  Further, the light source driving unit 97 changes the area of the apertures of the apertures 34a, 34b, 96 under a predetermined observation mode under the control of the processor device 90, so that the broadband light BB, B narrowband light Bn1, B excitation is performed. The amount of light Bn4 is controlled.

With each configuration described above, the light source device 88 emits the broadband light BB in the normal observation mode, and the mixed light of the broadband light BB and the B narrowband light Bn1 in the E, M1 to M3 modes (hereinafter simply referred to as first mixed light). BB and Bn1 are emitted, mixed light (hereinafter simply referred to as second mixed light) BB and Bn4 of the broadband light BB and B excitation light Bn4 is emitted in the AFI mode, and B narrowband light Bn1 is emitted in the low O ₂ mode. .About.Bn3 are sequentially emitted.

  The electronic endoscope 89 has basically the same configuration as the electronic endoscope 11 of the first embodiment except that a half mirror 98 and a high sensitivity (EM: Electron Multiplying) CCD 99 are provided.

  The half mirror 98 is disposed between the zoom lens 42 and the CCD 44. The half mirror 98 transmits a part of the light incident through the zoom lens 42 as it is and reflects a part of the incident light. The light transmitted through the half mirror 98 enters the CCD 44 and the light reflected by the half mirror 98 enters the EMCCD 99. When the amount of light incident on the half mirror 98 is 100, the ratio between the amount of light incident on the CCD 44 and the amount of light incident on the EMCCD 99 is about 50:50.

  The EMCCD 99 operates in the AFI mode. The EMCCD 99 has higher sensitivity performance than a normal CCD by amplifying a signal charge with an electron multiplication register, and is therefore suitable for imaging weak autofluorescence. Similarly to the CCD 44, the EMCCD 99 outputs an imaging signal to the AFE 45 at a predetermined frame rate based on a drive signal from the imaging control unit 46.

The CCD 44 outputs each color imaging signal by photoelectric conversion in each observation mode other than the low O ₂ mode as in the first embodiment. In the low O ₂ mode, the CCD 44 sequentially inputs B narrowband lights Bn1 to Bn3, respectively. The B1-B3 narrowband imaging signal is output after photoelectric conversion. The AFE 45 converts each color imaging signal or each narrow-band imaging signal output from the CCD 44 and the autofluorescence imaging signal output from the EMCCD 99 into a digital imaging signal and outputs the digital imaging signal to the DSP 55.

The processor device 90 has basically the same configuration as the processor device 12 of the first embodiment except that the processor device 90 includes the CPU 101. The DSP 55 appropriately performs image processing on each color imaging signal or each narrow-band imaging signal and autofluorescence imaging signal input from the AFE 45, and normal / special light image data or B1-B3 narrowband image data, autofluorescence image. Generate data. Specifically, normal image data is generated in the normal observation mode, special light image data is generated in the E, M1 to M3 modes, normal image data and autofluorescence image data are generated in the AFI mode, and the low O ₂ mode is generated. Sometimes B1-B3 narrowband image data is generated. Each of these image data is stored in the frame memory 56.

As shown in FIG. 18, the memory 53 stores a selection table 103 and an execution table 104. The selection table 103 is basically the same as the selection table 65 of the first embodiment, but whether the “AFI mode” and the “low O ₂ mode” are the preferred observation modes for each observation condition. Is set. The AFI mode is a preferred observation mode under all observation conditions. In addition, the low O ₂ mode is a preferable observation mode regardless of the magnification / non-magnification observation when the site to be observed is the esophagus E.

The execution table 104 is basically the same as the execution table 66 of the first embodiment, but the light amount ratio in the AFI mode and the low O ₂ mode, the color channel assignment, and whether or not the HPF process is executed are set. Has been. The light quantity ratio is set to BB: Bn4 = α: β in the AFI mode, and α and β are determined by experiments, simulations, and the like. In the low O ₂ mode, the light amount ratio is not adjusted, so the light amount ratio is blank.

Further, in the AFI mode and the low O ₂ mode, the color channel allocation is set to, for example, normal allocation and the HPF processing is not performed. However, these may be changed as appropriate.

  The CPU 101 functions as a suitable observation mode selection unit 106, a light source control unit 107, an image generation unit 108, and a display control unit 109 in addition to the observation condition determination unit 69 and the HPF processing unit 73 of the first embodiment.

  Based on the determination result of the observation condition determination unit 69, the suitable observation mode selection unit 106 refers to the selection table 103, selects a suitable observation mode from the seven observation modes, and displays the selection result on the display control unit 109. Send to.

  The light source control unit 107 refers to the execution table 104 and controls the light source driving unit 97 in accordance with the observation mode selected by the mode switch 59, so that the type of illumination light emitted from the light source device 88, Switch the amount of light.

The image generator 108 operates in the low O ₂ mode. The image generation unit 108, based on the B1 to B3 narrowband image data stored in the frame memory 56, blood vessel depth image data obtained by distinguishing and imaging the surface blood vessel, the middle blood vessel, and the deep blood vessel with different colors, Oxygen saturation image data obtained by imaging oxygen saturation information in a blood vessel is generated. For the method of generating the blood vessel depth image data and the elementary saturation image data, refer to Japanese Patent Application No. 2010-132964 filed by the present applicant. The blood vessel depth image data and the oxygen saturation image data are stored in the frame memory 56.

The display control unit 109 is basically the same as the display control unit 72 of the first embodiment, and refers to the execution table 104 to display the display control circuit 58 according to the observation mode selected by the mode switch 59. And the observation image is displayed on the monitor 14. However, the display control unit 109 causes the monitor 14 to display an observation image obtained by combining the normal image and the autofluorescence image based on the normal image data and the autofluorescence image data stored in the frame memory 56 in the AFI mode. Further, the display control unit 109 displays the blood vessel depth image and the oxygen saturation image on the monitor 14 based on the blood vessel depth image data and the oxygen saturation image data stored in the frame memory 56 in the low O ₂ mode. .

In addition, the display control unit 109 controls the GUI display unit 58a to synthesize and display the GUI image 62 indicating the selection result of the preferred observation mode selection unit 106 on the observation image. As shown in FIG. 19, when the site to be observed is the esophagus E, a GUI image 62 indicating the AFI mode and the low O ₂ mode is displayed on the monitor 14 regardless of non-magnification observation and magnification observation. As shown in FIG. 20, when the site to be observed is cardia C or stomach S, the GUI image 62 indicating the AFI mode is displayed regardless of non-magnification observation and magnification observation, but low O ₂ The GUI image 62 indicating the mode is not displayed. Note that the display of the GUI image 62 indicating other observation modes is the same as that in the first embodiment, and a description thereof will be omitted.

Next, the operation of the endoscope system 87 having the above configuration will be described with reference to the flowchart shown in FIG. Here, since the process flow from the inspection preparation process to the presence / absence of switching of the observation mode is basically the same as that of the first embodiment shown in FIG. 9, the description thereof is omitted here. Note that the GUI image 62 indicating the AFI mode is displayed under all observation conditions, and the GUI image 62 indicating the low O ₂ mode is displayed only when the site to be observed is the esophagus E.

[Switch to AFI mode]
When the mode switch 59 is switched from the normal observation mode to the AFI mode, for example, based on the GUI image 62 displayed on the monitor 14, the light source control unit 107 sets the light source driving unit 97 to the light source driving unit 97 based on the execution table 104. On the other hand, an excitation light irradiation command including information on the light amount ratio (BB: Bn4 = α: β) is issued. Further, the CPU 101 controls the photographing control unit 46 to operate the EMCCD 99.

  In response to the excitation light irradiation command from the light source control unit 107, the light source driving unit 97 turns on the fourth blue LD 95 and controls the diaphragms 34a and 96 to transmit broadband light from the broadband light source 30 and the fourth blue LD 95, respectively. BB and B excitation light Bn4 is emitted at a light quantity ratio BB: Bn4 = α: β. As a result, the second mixed light BB and Bn4 are irradiated to the observation site, and the second mixed light BB and Bn4 reflected and scattered by the observation site are incident on the CCD 44 and the EMCCD 99, respectively.

  The respective imaging signals output from the CCD 44 and the EMCCD 99 are stored in the frame memory 56 as normal image data and autofluorescence image data after passing through the AFE 45 and the DSP 55. Next, the display control unit 109 refers to the execution table 104 and determines normal allocation as color channel allocation, and then issues a self-fluorescent image display command to the display control circuit 58. In addition, the display control unit 109 issues a GUI image display command to the GUI display unit 58a based on the selection result of the preferred observation mode selection unit 106. As a result, the observation image obtained by combining the normal image and the autofluorescence image and the GUI image 62 are displayed on the monitor 14.

[Switch to low O ₂ mode]
On the other hand, when the mode switch 59 is switched from the normal observation mode to the low O ₂ mode, for example, the light source control unit 107 issues a narrowband light irradiation command to the light source driving unit 97 based on the execution table 104. To emit.

  The light source driving unit 97 receives the narrow band light irradiation command from the light source control unit 107 and turns off the broadband light source 30. Next, the light source driving unit 97 repeatedly executes a process of sequentially turning on the first to third blue LDs 92 to 94 for a predetermined time. As a result, the B narrowband light Bn1, the B narrowband light Bn2, the B narrowband light Bn3, the B narrowband light Bn1,.

  Each of the light beams Bn1 to Bn3, Bn1... Reflected / scattered at the observation site is sequentially incident on the CCD 44 and subjected to photoelectric conversion. Each of these lights also enters the EMCCD 99, but the EMCCD 99 is not used and is not used for imaging.

  The B1 to B3 narrowband imaging signal output from the CCD 44 is stored in the frame memory 56 as B1 to B3 narrowband image data after passing through the AFE 45 and the DSP 55. When the B1 to B3 narrowband image data is stored in the frame memory 56, the image generation unit 108 reads out each of these narrowband image data from the frame memory 56 and generates blood vessel depth image data and oxygen saturation image data. To do. These blood vessel depth image data and oxygen saturation image data are stored in the frame memory 56.

  Next, the display control unit 109 refers to the execution table 104 and determines normal allocation as color channel allocation, and then issues a blood vessel depth image and oxygen saturation image display command to the display control circuit 58. In addition, the display control unit 109 issues a GUI image display command to the GUI display unit 58a based on the selection result of the preferred observation mode selection unit 106. As a result, the blood vessel depth image, the oxygen saturation image, and the GUI image 62 are displayed on the monitor 14.

[Switch to another observation mode]
The display processing of the observation image and the GUI image 62 when switching to the observation mode other than the AFI mode and the low O ₂ mode is the same as that in the first embodiment, and thus the description thereof is omitted. Although not shown in the flowchart of FIG. 21, the operation of the EMCCD 99 is stopped when switching from the AFI mode to another observation mode. When switching from the low O ₂ mode to another observation mode, the broadband light source 30 is turned on.

  As described above, also in the endoscope system 87 according to the third embodiment, the GUI image 62 indicating the preferred observation mode corresponding to the observation condition is displayed on the monitor 14 together with the observation image, and thus the same effect as the first embodiment. Is obtained.

  In the third embodiment, the first to fourth blue LDs 92 to 95 are used as the light sources of the lights Bn1 to Bn4. For example, a broadband light source different from the broadband light source 30 and the wavelength band of transmitted light are controlled. The light Bn1 to Bn4 may be selectively emitted using a wavelength tunable element such as an etalon or a liquid crystal tunable filter (see Japanese Patent No. 4504078 and Japanese Patent Application Laid-Open No. 2010-2224011).

  In the third embodiment, the fourth blue LD 95 is used as the light source for the excitation light in the AFI mode. Good.

[Fourth Embodiment]
Next, an endoscope system 111 according to a fourth embodiment of the present invention will be described with reference to FIG. In the first embodiment, the description has been given by taking the type of site to be observed and the presence or absence of execution of magnification observation as examples of the observation conditions. However, in the endoscope system 111, the operation of the doctor on the electronic endoscope 11 is also performed. It is included in the observation conditions.

  The endoscope system 111 includes an electronic endoscope 112, a processor device 113, and a light source device 13. In addition, the same code | symbol is attached | subjected about the same thing as the said 1st Embodiment and a structure, and the description is abbreviate | omitted.

  The electronic endoscope 112 has basically the same configuration as the electronic endoscope 11 of the first embodiment, except that the liquid feeding mechanism 115 and the suction mechanism 116 are provided. The liquid feeding mechanism 115 includes a liquid feeding tank, a liquid feeding channel, a liquid feeding pump, and the like (not shown), and various diagnostic dyes are inserted into the distal end of the insertion portion in response to pressing operation of the liquid feeding button 22a constituting the operation button 22. It sprays from the part 16a to an observed site. The suction mechanism 116 includes a suction channel (not shown), a suction pump, and the like, and sucks various body fluids, body filth, and the like from the distal end portion 16a of the insertion portion in response to a pressing operation of the suction button 22b constituting the operation button 22.

  The processor device 113 is the first embodiment except that the selection table 118 different from the first embodiment is stored in the memory 53 and the CPU 119 functions as an observation condition determination unit 120 different from the first embodiment. This is basically the same configuration as the processor device 12 of the embodiment.

  In the selection table 118, the observation conditions including the type of the region to be observed and the enlargement / non-magnification observation, as well as the operation type of the doctor, and the preferred observation mode under each observation condition are stored in association with each other. Yes. The types of doctor operations referred to here are pigment spraying operations and suction operations.

  The observation condition discriminating unit 120 is basically the same as the observation condition discriminating unit 69 of the first embodiment, but by further monitoring the operation of the operation button 22 and the operation of the liquid feeding mechanism 115 and the suction mechanism 116, The type of doctor operation is determined. Then, the observation condition determination unit 120 sequentially sends the observation condition determination result including the type of the site to be observed, the presence / absence of magnified observation, and the type of doctor operation to the preferred observation mode selection unit 70.

  The suitable observation mode selection unit 70 selects a suitable observation mode with reference to the selection table 118 based on the determination result input from the observation condition determination unit 120. Note that the processing after the selection of the preferred observation mode is the same as that in the first embodiment shown in FIG.

  In the fourth embodiment, pigment spraying and suction are discriminated as doctor operations, but other doctor operations such as air feeding operations other than these are discriminated, and a suitable observation mode is selected based on the discrimination results. Also good. Further, during the suction operation, the type of body fluid to be sucked (for example, bile or gastric fluid) is determined based on the determination result of the type of the site to be observed and the analysis result of the image data stored in the frame memory 56. Thus, a suitable observation mode may be selected according to the type of body fluid to be sucked.

  In each of the embodiments described above, the HPF processing unit 73 performs HPF processing on the image data in order to further emphasize the surface blood vessels in the observation image. For example, the color of the blood vessels and mucous membranes in the observation image is changed. Further enhancement of superficial blood vessels using various blood vessel enhancement processing methods, such as performing color enhancement processing to make it easier to see blood vessels with a difference, and image structure enhancement processing such as sharpness processing and contour enhancement. May be.

  In each of the above embodiments, in the E, M1 to M3 modes, mixed light of the B narrowband light Bn and the broadband light BB is irradiated to the observation site. For example, instead of the broadband light BB, the wavelength of 500 nm to 600 nm is irradiated. Green narrow band light may be used. The present invention can also be applied to a case where mixed light of three or more types of light is emitted at different light quantity ratios in the E, M1-M3 mode, the AFI mode, or the like.

  The observation condition discriminating units 57 and 120 of each of the above embodiments discriminate the type of the observation site irradiated with the illumination light by analyzing the image data, but the type of the observation site is determined using various methods. It may be determined. For example, the type of the site to be observed can be determined based on the detection result of the PH of the site to be observed (see Japanese Patent No. 3321235). Further, the type of the site to be observed can also be determined using various position detection methods for detecting the position of the insertion portion distal end portion 16a in the patient body, for example, using a computed tomography (CT) apparatus. Furthermore, the type of the site to be observed may be determined by simple pattern recognition such as the shape inside the esophagus E and stomach S and the shape of the cardia C.

  Further, when the esophagus E where the superficial blood vessels gather and the cardia C where the mid-deep blood vessels gather are the sites to be observed, the type of the site to be observed is discriminated using the pattern and density of the superficial blood vessels and the mid-thick blood vessels as landmarks May be.

  In each of the above-described embodiments, description has been made by taking the type of site to be observed, non-magnification observation / magnification observation, and doctor operation (fourth embodiment) as examples of observation conditions. Conditions may be added.

  In each of the above embodiments, various illumination lights are emitted from the light source device to the electronic endoscope. However, various light sources such as a broadband light source and a blue LD may be provided in the insertion portion distal end portion 16a.

  In each of the above-described embodiments, the GUI image 62 is synthesized and displayed on the observation image as the selection result of the suitable observation mode corresponding to the observation conditions. However, the selection result of the suitable observation mode in various display modes such as text, list, and pop-up, for example. May be displayed. In addition, the selection result of the preferred observation mode may be displayed other than the monitor 14.

  In each of the above-described embodiments, the GUI image 62 is synthesized and displayed as an observation image as a result of selection of the preferred observation mode corresponding to the observation conditions. However, when there are a plurality of preferred observation modes, a particularly preferred preferred observation mode (for example, The E mode for the esophagus E, the M1 mode for the cardia C, and the M2 mode for the stomach S may be distinguished from each other.

  In each of the above embodiments, the endoscope system for observing surface blood vessels, autofluorescence observation, oxygen saturation and blood vessel depth has been described as an example, but infrared light observation (Infra Red Imaging) The present invention can be applied to an endoscope system used for various special light observations such as photodynamic diagnosis.

10, 80, 87, 111 Endoscope system 11, 89, 112 Electronic endoscope 12, 81, 90, 113 Processor unit 13, 88 Light source unit 14 Monitor 30 Broadband light source 31 Blue LD
34a, 34b Aperture 42 Zoom lens 44 CCD
54, 101, 119 CPU
58a GUI display unit 65, 103, 118 Observation mode selection table 66, 82, 104 Observation mode execution table 69, 120 Observation condition determination unit 70, 106 Suitable observation mode selection unit 71, 107 Light source control unit 72, 109 Display control Part 73 HPF processing part 92-95 1st-4th blue LD

Claims (15)

In an endoscope system that images an observation site in a subject by an endoscope and generates an observation image ,
A plurality of types of observation modes for generating the observation images having different aspects with respect to the same site to be observed , and types of illumination light used for acquiring image data corresponding to each observation mode, the amount of light, and the image data Storage means for storing a correspondence relationship with image processing to be performed,
An observation condition discriminating means for discriminating an observation condition including at least one of the type of the site to be observed and the type of operation on the endoscope;
In accordance with the observation conditions determined by the observation condition determination means, preferred observation mode selection means for selecting a suitable observation mode suitable for the observation conditions from a plurality of types of the observation modes,
Display means for displaying the preferred observation mode;
Depending on the mode switching operation to switch to the preferred viewing mode, the type of the illumination light corresponding to the switched preferred observation mode, the observation-mode switching unit Ru switched to the amount and the image processing,
An endoscope system comprising: The endoscope system according to claim 1, wherein the display unit does not display the observation mode that has not been selected by the preferred observation mode selection unit. Includes a light source that selectively emits one of a plurality of types of the illumination light, the endoscope, the illumination light emitted from the light source, the distal end of the insertion portion to be inserted into the inside of the subject And irradiating the observed site from the part,
Wherein the observation mode, including a normal observation mode Use of white broadband light as the illumination light, a special light observation mode to be used as the illumination light narrowband light is limited to a specific wavelength band used for the observation special light is The endoscope system according to claim 1 or 2 , wherein the endoscope system is configured as described above. Wherein the special light observation mode, claims, characterized in that there are multiple modes using at least the narrow plurality including band light a plurality of the mixed light obtained by mixing in different quantity ratios light as each said illumination light 3. The endoscope system according to 3 . The endoscope system according to claim 4 , wherein the mixed light is a mixture of the narrowband light and the broadband light. In the special light observation mode, an operation reception unit that receives the adjustment operation of the light amount ratio, and a light amount ratio control that adjusts the light amount ratio by controlling the light source according to the adjustment operation received by the operation reception unit The endoscope system according to claim 4 or 5 , further comprising: means. A zoom lens, a zoom mechanism that moves the zoom lens in the direction of the optical axis, and an image of the observation site are imaged through the zoom lens at a distal end portion of an insertion portion that is inserted into the subject of the endoscope. And an image sensor,
Wherein the viewing conditions, the endoscope system according to any one of claims 1 to 6, characterized in that that contains the presence or absence of magnifying observation of the target site by the zoom lens. The storage means stores a correspondence relationship between the observation conditions and the preferred observation mode ,
The said suitable observation mode selection means selects the said suitable observation mode with reference to the said memory | storage means based on the determination result of the said observation condition determination means, The any one of Claim 1 thru | or 7 characterized by the above-mentioned. Endoscope system. The operation for the endoscope includes a spraying operation for spraying liquid from the distal end portion of the insertion portion of the endoscope to the observed site, and a suction operation for sucking body fluid in the observed site from the distal end portion. the endoscope system according to any one of claims 1 to 8, characterized in that it contains. A blood vessel enhancement processing means for performing blood vessel enhancement processing for emphasizing a blood vessel of the observation site on the image data of the observation image;
The endoscope system according to any one of claims 1 to 9, wherein a type of the observation mode varies depending on whether or not the blood vessel enhancement processing is performed. The endoscope system according to claim 10 , wherein the blood vessel enhancement processing unit performs high-pass filter processing for enhancing high-frequency components on the image data as the blood vessel enhancement processing. The display means, the endoscope system according to any one of claims 1 to 11, characterized in that the display and the observation image, the synthesized composite image and the preferred viewing mode. The display means, the endoscope system according to any one of claims 1 to 12, characterized in that displaying the preferred viewing mode as a graphical user interface (GUI) image. In an operation method of an endoscope system that images an observation site in a subject with an endoscope to generate an observation image having a different aspect for each type of observation mode,
An observation condition determining step of determining an observation condition including at least one of a type of the observed region and an operation type on the endoscope by an observation condition determining unit ;
In accordance with the observation condition determined in the observation condition determination step, a suitable observation mode selection step for selecting a suitable observation mode suitable for the observation condition from a plurality of types of the observation modes by a suitable observation mode selection unit ,
A display step of displaying by the display means the preferred viewing mode,
In accordance with the mode switching operation, the observation mode switching means switches to the preferred observation mode and switches to the type of illumination light, the amount of light, and image processing corresponding to the switched preferred observation mode;
A method of operating an endoscope system, comprising: 15. The operation method of the endoscope system according to claim 14, wherein the display step does not display the observation mode that has not been selected by the preferred observation mode selection unit.

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