JP2010082041A - Electronic endoscope system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To prevent a laser beam from being carelessly emitted when using the laser beam as excitation light for imaging a fluorescent image. <P>SOLUTION: In the electronic endoscope system for emitting the laser beam from a scope distal end through the light guide 170 and illumination lens 150 of a laparoscope 100 from a light source unit 300 having a laser beam source 312 for imaging the fluorescent image, a pressure detector 152 is disposed at the insertion part distal end 100A of the laparoscope 100. A CPU 210 inside a processor 200 turns on the power of the laser beam source 312 only when the scope distal end is inserted to a subject (abdomen) to which pneumoperitoneum is performed by a pneumoperitoneum apparatus 500 and a detection signal indicating an intraperitoneal pressure equal to or more than a stipulated pressure is inputted from the pressure detector 152, and thus, prevents the laser beam from being erroneously emitted when the scope distal end is not inserted to the subject. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to an electronic endoscope system, and more particularly to an electronic endoscope system capable of capturing a fluorescent image.

  By injecting a labeling reagent such as indocyanine green (ICG) into the living body, irradiating excitation light in a specific wavelength range for causing the labeling reagent to emit light, and photographing the living tissue emitted by this excitation light, Attention has been focused on a system for acquiring a fluorescent image that can observe blood vessels, lesions, and the like located on the lower layer side of the surface of a living tissue (Patent Documents 1 and 2).

  In endoscopic treatment (surgery) for humans and animals, it is necessary to pay sufficient attention not to damage the blood vessels, but check for blood vessels that exist beyond a certain depth from the body tissue surface of the subject. There is a risk of damaging blood vessels (bleeding risk).

In an endoscopic operation, the operation can be supported by displaying a fluorescent image that enables observation of blood vessels and the like located on the lower layer side of the surface of a living tissue.
JP 2001-299676 A JP 2007-244746 A

  By the way, near-infrared laser light is used as excitation light in a specific wavelength region for causing the labeling reagent to emit light, and several milliwatts to several tens milliwatts (mW) in order to enable observation of deeper blood vessels. ) May be required.

  Therefore, if laser light is emitted from the distal end of the scope in a state where the endoscope scope is not inserted into the patient's body, there is a risk of accidentally entering the eye, which may cause damage to the retina.

  The present invention has been made in view of such circumstances. When laser light is used as excitation light for capturing a fluorescent image, the laser light can be prevented from being inadvertently emitted. An object of the present invention is to provide an electronic endoscope system capable of ensuring the safety of a mirror operator, surrounding surgical personnel, and a patient.

  In order to achieve the above object, the invention according to claim 1 is an electronic endoscope system including a laser light source and an endoscope scope that emits laser light generated from the laser light source from a distal end of the scope, When detecting that the scope tip of the endoscope scope is inserted into the subject, and detecting that the scope tip of the endoscope scope is inserted into the subject by the detecting means And an interlocking means that enables laser light to be emitted from the distal end of the scope of the endoscope scope.

  That is, only when the endoscope scope is inserted into the subject, laser light can be emitted from the scope tip, so that when the endoscope scope is not inserted into the subject, the laser light is accidentally emitted. The danger of light emission is avoided.

  The electronic endoscope system according to claim 1, wherein the endoscope scope is a laparoscope that is inserted into an abdominal cavity inhaled by an insufflation apparatus, and the detection unit Includes pressure detection means provided in the laparoscope scope or pressure detection means provided in an insufflation apparatus connected to an air supply tube of the laparoscope scope, and the pressure detection means is defined to be higher than atmospheric pressure. When a pressure equal to or higher than the pressure is detected, it is determined that the distal end of the scope of the laparoscope is inserted into the subject.

  When the laparoscopic scope is inserted into the abdominal cavity normally inhaled by the insufflation apparatus, the pressure detecting means detects an intra-abdominal pressure higher than the atmospheric pressure. Therefore, it is possible to determine whether or not the scope tip is inserted into the subject based on the detection result of the pressure detection means.

  According to a third aspect of the present invention, in the electronic endoscope system according to the first aspect, the detection means includes a light detection means disposed in at least an insertion portion of the endoscope scope that is inserted into the subject. In addition, when the light detection means detects a light amount equal to or less than a predetermined value, it is determined that the distal end of the scope of the endoscope scope is inserted into the subject.

  Since the inside of the subject is dark except for the portion illuminated by the scope tip, the scope of the endoscope scope is determined by the amount of light detected by the light detection means disposed in the insertion portion inserted into the subject. It can be determined whether or not the tip is inserted into the subject.

  According to a fourth aspect of the present invention, in the electronic endoscope system according to the third aspect, the light detecting means is disposed at a position where light emitted from a scope tip of the endoscope scope does not reach. It is a feature.

  The electronic endoscope system according to any one of claims 1 to 4, wherein the interlock means is configured such that a scope tip of the endoscope scope is inserted into the subject by the detection means. The laser light source is turned on / off according to whether or not it has been detected. Needless to say, an operation unit for manually turning on / off the power source of the laser light source may be provided.

  As shown in claim 6, in the electronic endoscope system according to any one of claims 1 to 5, the laser light source has a near-infrared region as excitation light for causing a labeling reagent administered to a subject to emit light. The endoscope scope generates a laser beam, the endoscope scope receives the laser beam, and emits the laser beam from the distal end of the scope; and an imaging unit that images the subject irradiated with the laser beam. And image processing means for generating a fluorescence image corresponding to the near-infrared region based on an image signal output from the imaging means of the endoscope scope and outputting the fluorescence image to a monitor device.

  That is, the laser light is used as excitation light for emitting the labeling reagent administered to the subject, and imaging and fluorescent images of the living tissue emitted by the excitation light by the endoscope scope and image processing means. Is generated. With this fluorescent image, blood vessels and the like located on the lower layer of the surface of the living tissue can be observed, which is particularly effective for endoscopic surgery.

  The electronic endoscope system according to claim 6, further comprising a visible light source that generates illumination light in a visible light wavelength range, wherein the endoscope scope is generated from the visible light source. An illumination optical system for receiving illumination light and irradiating the subject from the distal end of the scope; and an imaging means for imaging the subject irradiated with the illumination light, wherein the image processing means is the endoscope scope Based on the image signal output from the imaging means, a normal image corresponding to the wavelength range of visible light is generated and output to the monitor device.

  According to this electronic endoscope system, it is possible to observe a normal image (image on the surface of a living tissue) of a subject illuminated with visible light together with the fluorescent image.

  According to the present invention, in an electronic endoscope system that uses laser light as excitation light for capturing a fluorescent image, laser light is emitted from the distal end of the scope only when the endoscope scope is inserted into a subject. Therefore, when the endoscope scope is not inserted into the subject, the risk of accidental laser light emission can be avoided, and the operation of the endoscope operator, surrounding surgical personnel and patients can be avoided. Safety can be ensured.

  Hereinafter, preferred embodiments of an electronic endoscope system according to the present invention will be described with reference to the accompanying drawings.

<Appearance of electronic endoscope system>
FIG. 1 is an external view showing an embodiment of an electronic endoscope system according to the present invention.

  As shown in FIG. 1, the electronic endoscope system 10 mainly includes a laparoscope scope 100, which is a kind of endoscope scope, a processor 200, a light source device 300, and a monitor device 400. Note that the processor 200 may be configured to incorporate the light source device 300.

  The laparoscopic scope 100 is detachably attached to the processor 200 and the light source device 300 via an electrical connector 110 and a light guide (LG) connector 120, respectively. An image showing the subject imaged by the laparoscope 100 is appropriately subjected to image processing by the processor 200 and then output to the monitor device 400, where it is observed by the endoscope operator.

  FIG. 2 is a schematic view of a laparoscopic operation using the laparoscopic scope 100. In laparoscopic surgery, several holes are opened in the abdominal wall, and a treatment tool such as an insertion portion distal end 100A of the laparoscopic scope 100, an electric scalpel 30 used for endoscopic surgery, and forceps is inserted through the trocar 20. Then, the abdominal wall is inflated by introducing insufflation gas from an insufflation apparatus 500 (FIG. 3) described later.

  The endoscope operator advances the operation by operating the treatment tool while observing the operation target site imaged by the laparoscope scope 100 with the monitor device 400.

<Internal configuration of electronic endoscope system>
FIG. 3 is a block diagram showing an internal configuration of the electronic endoscope system 10.

[Laparoscopic scope]
An objective lens 130, an imaging device (CCD) 140, an illumination lens 150, and a pressure detector 152 are disposed at the distal end 100 </ b> A of the laparoscope scope 100.

  The objective lens 130 forms an image of the subject on the light receiving surface of the CCD 140, and the CCD 140 converts the subject image formed on the light receiving surface into an electric signal by each light receiving element. The CCD 14 of this embodiment is a color CCD in which three primary color red (R), green (G), and blue (B) color filters are arranged for each pixel in a predetermined arrangement (Bayer arrangement, honeycomb arrangement). It is.

  Further, inside the laparoscopic scope 100, a wiring 160 for driving the CCD 140 and taking out the CCD output is provided, and a light guide 170 is provided.

  The pressure detector 152 detects the pressure in the abdominal cavity where the pneumoperitone gas is injected by the pneumoperitoneum apparatus 500, and outputs a pressure signal indicating the detected pressure to the processor 200.

  One end 170 </ b> A of the light guide 170 is connected to the light source device 300 via the LG connector 120, and the other end 170 </ b> B of the light guide 170 faces the illumination lens 150. The light emitted from the light source device 300 is emitted from the illumination lens 150 via the light guide 170 and illuminates the visual field range of the objective lens 130.

[Processor]
The processor 200 mainly includes a central processing unit (CPU) 210, an analog front end (AFE) 220, an image input controller 222, a normal image processing unit 224, a fluorescence image processing unit 226, an image composition unit 230, a CCD driver 240, a timing. A generator (TG) 242, a character generator (CG) 244, a memory 246, a video output unit 248, and an operation unit 250 are included.

  The CPU 210 has a built-in program ROM in which various data necessary for control are recorded in addition to the control program executed by the CPU 210. The CPU 210 reads out a control program recorded in the program ROM to the memory 246 based on an instruction input such as a photographing instruction from the operation unit 250, and controls each unit by sequentially executing the program. The memory 246 is used as a program execution processing area, a temporary storage area for image data, and various work areas.

  The CCD 140 in the laparoscope scope 100 outputs the charges accumulated in each pixel as a serial image signal line by line in synchronization with the vertical transfer clock and horizontal transfer clock supplied from the TG 242 via the CCD driver 240. . The CPU 210 controls the driving of the CCD 140 by controlling the TG 242.

  The operation unit 250 includes a power switch, a switch for instructing start and end of photographing, a switch for instructing air / water supply, and the like.

  The image signal output from the CCD 140 is an analog signal, and this analog image signal is taken into the AFE 220. The AFE 220 includes a correlated double sampling circuit (CDS), an automatic gain control circuit (AGC), and an AD converter (ADC). The CDS removes noise contained in the image signal, the AGC amplifies the noise-removed image signal with a predetermined gain, and the ADC converts the analog image signal into a digital image having a gradation width of a predetermined bit. Convert to signal.

  The image input controller 222 has a built-in line buffer having a predetermined capacity, and stores an image signal for one frame output from the AFE 220. The image signal for one frame accumulated in the image input controller 222 is stored in the memory 246 via the bus 256.

  In addition to the CPU 210, the memory 246, and the image input controller 222, the normal image processing unit 224, the fluorescent image processing unit 226, the image composition unit 230, the video output unit 248, and the like are connected to the bus 256. It is possible to send and receive information to and from each other.

  The image signal for one frame stored in the memory 246 is taken into the normal image processing unit 224 or the fluorescence image processing unit 226 and subjected to necessary image processing. The images processed by the normal image processing unit 224 and the fluorescence image processing unit 226 are combined by the image combining unit 230. Details of the normal image processing unit 224, the fluorescence image processing unit 226, and the image composition unit 230 will be described later.

  The synthesized image synthesized by the image synthesis unit 230 is converted into a video signal for the monitor device 400 by the video output unit 248 and is output to the monitor device 400.

[Light source device]
The light source device 300 includes a visible light source 310 that mainly generates white light, a laser light source 312 that generates laser light in a specific wavelength region (near infrared region), a rotary filter 320, an aperture 330, a condensing lens 340, a half mirror 342, The reflection mirror 344, a motor drive circuit 350, a motor 360, and an automatic light amount adjustment circuit (ALC) 370 are provided and have a function of causing visible light and laser light to enter the light guide 170 alternately.

  As the visible light source 310, for example, a halogen lamp can be used. White light emitted from the halogen lamp has a wavelength range of 400 nm to 1800 nm. The rotary filter 320 transmits only visible light according to the rotational position.

  FIG. 4 is a plan view of the rotary filter 320. As shown in the figure, the rotary filter 320 is provided with an infrared cut filter 322. When the infrared cut filter 322 is positioned in front of the light source 310, the rotary filter 320 has a visible light (400 nm). Only ˜700 nm).

  The motor drive circuit 350 outputs a drive signal to the motor 360, rotates the rotary filter 320 at a speed of 30 times / second, and at the same time an infrared cut filter 322 in the range of 180 ° in synchronization with the vertical synchronization signal from the TG 242. And the phase are controlled so that the light-shielding portion in the range of 180 ° is switched.

  The visible light that has passed through the rotary filter 320 is guided to the end face of the one end 170 </ b> A of the light guide 170 via the diaphragm 330, the condenser lens 340, and the half mirror 342.

  As the laser light source 312, a semiconductor laser that emits laser light in the near infrared region near 800 nm (for example, several milliwatts to several tens milliwatts (mW)) can be used. This laser light is incident on the end face of one end 170 </ b> A of the light guide 170 via the reflection mirror 520 and the half mirror 530.

  The laser light source 312 is controlled to emit laser light intermittently in synchronization with the vertical synchronization signal from the TG 242. That is, the light emission period of the laser light source 312 is controlled so as to be synchronized with the light shielding period in which the white light emitted from the visible light source 310 is shielded by the rotary filter 320.

  Further, the power source of the laser light source 312 is configured to be turned on / off by a command from the CPU 210 of the processor 200. The details of the power on / off control of the laser light source 312 will be described later. Further, the light source device 300 is provided with an operation unit (not shown), and the power source of the laser light source 312 and the main power source of the light source device 300 can be turned on / off by this operation unit.

  The ALC 370 controls the diaphragm 330 based on the brightness information of the captured image applied from the CPU 210, and adjusts the amount of light incident on the light guide 170 so that the captured image is maintained at a constant brightness. This prevents halation or the like from occurring.

  When visible light is incident on the light guide 170 by the light source device 300 having the above configuration, the laparoscopic scope 100 can capture a color image (normal image) and the laser light (excitation light) is incident on the light guide 170. The laparoscopic scope 100 can take a fluorescent image of a biological tissue that emits fluorescence with laser light.

  In addition, a white light emitting diode can be used as the visible light source 310, and the rotary filter 320 and the like can be omitted by controlling the white light emitting diode on / off.

[Pneumoconiosis device]
The insufflation apparatus 500 includes a cylinder filled with insufflation gas such as carbon dioxide gas. The insufflation gas is supplied to the trocar 20 and the insufflation trocar (not shown) shown in FIG. 2 through an insufflation tube. It can be injected into the abdominal cavity.

  The insufflation apparatus 500 includes a pressure detector 502 for detecting intra-abdominal pressure, and controls insufflation and insufflation of insufflation gas so as to maintain a preset intra-abdominal pressure. Further, the pressure detector 152 outputs a pressure signal indicating the detected pressure to the processor 200.

[Method for obtaining fluorescent image including blood vessel image]
In order to obtain information in living tissue using light, it is necessary to avoid light in a wavelength range that is absorbed by the living tissue. As shown in FIG. 5, in the wavelength range of visible light of 700 nm or less, there is absorption of hemoglobin, and in the wavelength range of 1000 nm or more, there is water absorption, so light in this wavelength range cannot be used. Light in the wavelength range of 700 nm to 1000 nm (near infrared range) is referred to as a “biological spectroscopic window” because it passes through living tissue relatively well. In other words, the above-described excitation light in the near infrared region is light that permeates the living tissue relatively well.

  In order to observe the blood vessels inside the living tissue, a labeling reagent is administered to the subject, and a fluorescent image including a blood vessel image is taken by irradiating laser light (near-infrared excitation light). As the labeling reagent, a fluorescent reagent ICG (indocyanine green) having an excitation light wavelength of 785 nm and a fluorescence wavelength of 805 nm, and a fluorescent reagent Cy7 having an excitation light wavelength of 747 nm and a fluorescence wavelength of 776 nm can be used.

<First Embodiment>
In this embodiment, normal images and fluorescent images are taken alternately. When a fluorescent image is taken, the living tissue is irradiated with laser light as described above.

  FIG. 6 is a flowchart showing the first embodiment of the processing contents of the electronic endoscope system 10 according to the present invention.

  First, a labeling reagent is administered from the vein of the subject (step S10). Since the labeling reagent is metabolized and excreted in the body, it is necessary to administer the labeling reagent so as to keep the blood concentration constant.

  Further, pneumoperitoneum control is performed by injecting pneumoperitone gas into the abdominal cavity by the pneumoperitoneum apparatus 500 to inflate the abdominal wall (step S12). In the insufflation control, control is performed so that the intra-abdominal pressure is maintained at a preset value.

  Subsequently, the CPU 210 in the processor 200 inputs the detected pressure detected by the pressure detector 152 disposed at the insertion portion distal end 100A of the laparoscope scope 100 (step S14), and the input detected pressure is the specified pressure. It is determined whether or not this is the case (step S16).

  As the specified pressure, an appropriate pressure can be specified within a range that is higher than the atmospheric pressure by a predetermined pressure and lower than a pressure (for example, 10 mmHg) set in advance as an intra-abdominal pressure.

  When the pressure detected by the pressure detector 152 is equal to or higher than a specified value (in the case of “yes”), the CPU 210 determines that the scope tip of the laparoscope scope 100 is inserted into the subject. This is because when the laparoscopic scope 100 is inserted into the abdominal cavity normally inhaled by the insufflation apparatus 500, the pressure detector 152 detects an intra-abdominal pressure higher than the atmospheric pressure. . In this case, the laser light source 312 is turned on (step S18).

  On the other hand, if the pressure detected by the pressure detector 152 is less than the specified value (in the case of “no”), it is determined that the scope tip of the laparoscopic scope 100 is not inserted into the subject, and the laser light source 312 is turned off (step) S20).

  Thereby, only when the laparoscope scope 100 is inserted into the subject, laser light can be emitted from the distal end of the scope, and when the laparoscope scope 100 is not inserted into the subject, the laser light is erroneously emitted. So that you can avoid the danger.

  Subsequently, the normal image and the fluorescence image are alternately photographed for each frame in synchronization with the vertical synchronization signal (VD signal) having a period of 1/60 seconds (step S22). That is, visible light and laser light are alternately emitted from the light source device 300 and the subject is irradiated through the light guide 170 and the illumination lens 150. As a result, normal image exposure (photographing) and fluorescent image exposure (photographing) are alternately performed by the CCD 140.

  The normal image processing unit 224 shown in FIG. 3 performs normal image processing on the image signal (normal image) read from the CCD 140 when the normal image is captured (step S24). The normal image processing unit 224 includes a linear matrix circuit, a white balance correction circuit, a gamma correction circuit, a synchronization circuit, and the like. The normal image processing unit 224 performs signal processing of R, G, and B image signals input by these circuits, and performs normal image processing. The image signal is generated.

  On the other hand, the image signal (fluorescence image) read from the CCD 140 at the time of capturing the fluorescence image is subjected to fluorescence image processing by the fluorescence image processing unit 226 shown in FIG. 3 (step S26). The fluorescent image processing unit 226 first performs signal processing of R, G, and B image signals input by a gamma correction circuit, a synchronization circuit, and the like, and the R, G, and B images after the synchronization processing by the synchronization circuit. A luminance signal (image signal indicating a fluorescent image having only density information) is generated from the signal.

  The normal image and the fluorescence image generated as described above are combined by the image combining unit 230. As a combining method, a method of combining the normal image and the fluorescent image on one screen and a method of combining the fluorescent image on the normal image can be considered. In the latter case, it is necessary to give a pixel value only to a necessary part such as a blood vessel from the fluorescent image and to give a transparent attribute to the other part. According to this, only the blood vessel image can be pasted and synthesized on the normal image, and the portion without the blood vessel can be synthesized so that the normal image can be seen.

  The synthesized image synthesized by the image synthesis unit 230 as described above is output to the monitor device 400 via the video output unit 248 and displayed on the monitor device 400 (step S30).

  Next, it is determined whether or not the operation has been completed based on whether or not an operation end instruction has been input from the operation unit 250. If the operation has not been completed, the process proceeds to step S10. Ends this processing (step S32).

  Note that when the laser light source 312 is turned off, the CPU 210 may omit the fluorescence image processing in step S26 and the image composition processing in step S28.

  In this embodiment, the CPU 210 inputs the detected pressure detected by the pressure detector 152 disposed in the laparoscopic scope 100, and whether or not the scope tip is inserted into the subject based on the detected pressure. However, it may be determined whether or not the distal end of the scope is inserted into the subject based on the pressure detected by the pressure detector 502 provided in the pneumoperitoneum apparatus 500. In this case, an air supply tube (water supply tube) provided in the laparoscope scope 100 is connected to the pneumoperitoneum device 500 by a tube or the like, and the pressure detector 502 detects the intraabdominal pressure via the laparoscope scope 100. Like that.

<Second Embodiment>
In the first embodiment, the pressure detector 152 is disposed at the insertion portion distal end 100A of the laparoscope 100. However, in the second embodiment, instead of the pressure detector 152, FIG. As shown in FIG. 4, a photodetector 600 is provided. Other configurations are the same as those of the first embodiment.

  That is, the photodetector 600 that can detect the ambient light is disposed in the insertion portion that is inserted into the subject of the laparoscope scope 100. The light detector 600 is disposed at a position where the light emitted from the scope tip does not reach. In the example shown in FIG. 2, the photodetector 600 is disposed at a position corresponding to the approximate center of the trocar 20.

  Since ambient light does not enter the trocar 20, the light detector 600 cannot detect light when the laparoscope scope 100 is inserted into the trocar 20 (subject). Therefore, when the light detector 600 detects a light amount that is less than or equal to a preset specified value, it can be determined that the scope tip is inserted into the subject, and the light amount exceeding the specified value is detected. If it is, it can be determined that the distal end of the scope is not inserted into the subject and illumination light (ambient light) in the room or the like is detected.

  The CPU 210 determines whether or not the detected light amount is equal to or less than a specified value based on a detection signal indicating the detected light amount input from the photodetector 600. If the detected light amount is equal to or less than the specified value, the scope tip of the laparoscopic scope 100 is the subject. The laser light source 312 is turned on, and if the prescribed value is exceeded, it is determined that the scope tip of the laparoscopic scope 100 is not inserted into the subject, and the laser light source 312 is turned off. To.

<Modification of Second Embodiment>
In the second embodiment, the photodetector 600 is disposed in the laparoscope scope 100. However, in the modification of the second embodiment, the upper gastrointestinal endoscope scope 102 is shown in FIG. An optical detector 602 is disposed on the side.

  The light detector 602 is disposed at a position where light emitted from the distal end of the scope does not reach as in the second embodiment. In the example shown in FIG. 7, when the scope tip of the upper gastrointestinal endoscopic scope 102 is at a position for observing the stomach, the photodetector 602 is disposed at a position corresponding to the esophagus of the upper gastrointestinal endoscopic scope 102. To do. That is, since the illumination light at the time of observation of the stomach does not reach the esophagus, the light detector 602 cannot detect the light when the distal end of the scope of the upper gastrointestinal endoscope scope 102 is inserted into the subject. First, the amount of light detected by the photodetector 602 is less than the specified value.

[Others]
In the present invention, the laser light source is turned on / off according to whether or not the scope tip is inserted into the subject. However, the scope tip is continuously inserted into the subject for a certain period of time or longer. It is preferable to turn on the laser light source only when it is detected, and immediately turn off the laser light source when it is detected that the scope tip is not inserted into the subject.

  In this embodiment, when it is detected that the scope tip is not inserted into the subject, the power source of the laser light source is turned off. Instead of turning off the power source, laser light is emitted from the light source device. Interlock means for blocking by a mechanical shutter or the like may be provided so as not to occur.

  In the electronic endoscope system 10 of this embodiment, visible light and laser light are alternately incident on the light guide 170 of the laparoscope scope 100 from the light source device 300 and the laparoscope scope 100 having one CCD 140. However, the present invention is not limited to this, and the visible light and the laser light are separately incident on the two light guides separately. A normal image and a fluorescent image may be simultaneously captured by a laparoscope having two CCDs.

  FIG. 8 shows an example of the scope tip of a laparoscopic scope having two CCDs. The distal end portion of the laparoscopic scope 100 includes an objective lens 132, a dichroic prism 134, a low-frequency cut filter 136, and CCDs 142 and 144.

  Reflected light from the subject in which visible light and laser light are mixed enters the dichroic prism 134 through the objective lens 132. The dichroic prism 134 transmits light having a wavelength of 810 nm or more and reflects light (laser light) having a wavelength of 810 nm or less in a right angle direction, and the low-frequency cut filter 136 cuts light having a wavelength of 700 nm or less.

  Thus, the CCD 142 photoelectrically converts the subject image illuminated with visible light and outputs a CCD output 1, and the CCD 144 photoelectrically converts the subject image illuminated with laser light and outputs a CCD output 2. By performing image processing on these CCD output 1 and CCD output 2, a normal image and a fluorescence image can be acquired simultaneously.

  In addition, the imaging units such as the CCDs 142 and 144 may be a laparoscope of a type that is provided at the rear end of the laparoscope and guides the subject image using a relay lens or the like.

  Furthermore, in this embodiment, the case where the laparoscope scope and the upper gastrointestinal endoscope scope are used has been described. However, the present invention is not limited to this, and various endoscope scopes (small intestine endoscope, large intestine endoscope) can be used. Applicable to endoscopes, thoracoscopes, laryngoscopes, bronchoscopes, cystoscopes, cholangioscopes, arthroscopes, etc.) In short, anything that generates laser light to capture fluorescent images It can also be applied to.

  The present invention is not limited to the above examples, and it goes without saying that various improvements and modifications may be made without departing from the scope of the present invention.

FIG. 1 is an external view showing an embodiment of an electronic endoscope system according to the present invention. FIG. 2 is a schematic diagram of a laparoscopic operation using a laparoscopic scope. FIG. 3 is a block diagram showing an internal configuration of the electronic endoscope system. FIG. 4 is a plan view of the rotary filter. FIG. 5 is a graph showing the relationship between the wavelength of light and the light absorption rate of living tissue. FIG. 6 is a flowchart showing the first embodiment of the processing contents of the electronic endoscope system according to the present invention. FIG. 7 is a diagram used for explaining a modification of the second embodiment of the electronic endoscope system according to the present invention. FIG. 8 is a main part configuration diagram showing another example of a laparoscopic scope to which the present invention is applied.

Explanation of symbols

  DESCRIPTION OF SYMBOLS 10 ... Electronic endoscope system, 20 ... Trocar, 30 ... Electric knife, 100 ... Laparoscope scope, 102 ... Upper gastrointestinal endoscope scope, 140, 142, 144 ... CCD, 152, 502 ... Pressure detector, 170 ... Light guide, 200 ... Processor, 210 ... Central processing unit (CPU), 224 ... Normal image processing unit, 226 ... Fluorescence image processing unit, 300 ... Light source device, 310 ... Visible light source, 312 ... Laser light source, 320 ... Rotation filter, 400 ... monitor device, 500 ... pneumothorax device, 600,602 ... photodetector

Claims (7)

An electronic endoscope system having a laser light source and an endoscope scope for emitting laser light generated from the laser light source from the distal end of the scope,
Detecting means for detecting that a scope tip of the endoscope scope is inserted into a subject;
An interlocking means for allowing laser light to be emitted from the scope scope tip of the endoscope scope only when it is detected by the detection means that the scope scope tip of the endoscope scope has been inserted into the subject; ,
An electronic endoscope system comprising: The endoscopic scope is a laparoscopic scope that is inserted into the abdominal cavity inhaled by an insufflation apparatus,
The detection means includes pressure detection means provided in the laparoscope scope, or pressure detection means provided in an insufflation apparatus connected to an air supply tube of the laparoscope scope, and the pressure detection means is more than atmospheric pressure. 2. The electronic endoscope system according to claim 1, wherein when a pressure equal to or higher than a high specified pressure is detected, it is determined that the scope tip of the laparoscope is inserted into the subject.   The detection means includes light detection means disposed at least in an insertion portion of the endoscope scope that is inserted into the subject, and when the light detection means detects a light amount equal to or less than a predetermined value, the endoscope 2. The electronic endoscope system according to claim 1, wherein it is determined that the scope tip of the scope is inserted into the subject.   The electronic endoscope system according to claim 3, wherein the light detection unit is disposed at a position where light emitted from a scope tip of the endoscope scope does not reach.   The interlock means turns on / off the power of the laser light source according to whether or not the detection means detects that the scope tip of the endoscope scope is inserted into the subject. An electronic endoscope system according to any one of claims 1 to 4. The laser light source generates near-infrared laser light as excitation light for causing the labeling reagent administered to the subject to emit light,
The endoscope scope includes a light guide unit that receives the laser beam and emits the laser beam from a distal end of the scope, and an imaging unit that images the subject irradiated with the laser beam,
6. An image processing means for generating a fluorescence image corresponding to the near-infrared region based on an image signal output from an imaging means of the endoscope scope and outputting the fluorescence image to a monitor device. The electronic endoscope system according to any one of the above. It has a visible light source that generates illumination light in the visible wavelength range,
The endoscope scope includes an illumination optical system for receiving illumination light generated from the visible light source and irradiating the subject from a scope tip, and an imaging unit for imaging the subject irradiated with the illumination light. Have
The said image processing means produces | generates the normal image corresponding to the wavelength range of visible light based on the image signal output from the imaging means of the said endoscope scope, and outputs it to a monitor apparatus. The electronic endoscope system described in 1.

Images