JP5389426B2 - Optical probe device and operating method thereof - Google Patents

Description

The present invention relates to an optical probe device and an operating method thereof, and more particularly, to an optical probe device and an operating method thereof characterized by controlling expansion of a plurality of balloons provided at the tip of the optical probe.

  Conventionally, as an endoscope apparatus for observing the inside of a body cavity of a living body, an electronic endoscope apparatus that irradiates illumination light inside the body cavity of a living body, captures an image of reflected light reflected, and displays it on a monitor or the like is widely spread And used in various fields. Many endoscope apparatuses are provided with a forceps opening, and biopsy and treatment of tissue in the body cavity can be performed by a probe introduced into the body cavity via the forceps opening.

  On the other hand, in recent years, development of a tomographic image acquisition apparatus that acquires a tomographic image of a living body and the like without cutting a measurement target such as a biological tissue has been promoted. An optical tomographic imaging apparatus using an optical coherence tomography (Patent Document 1) is known.

  This OCT measurement is a measurement method that utilizes the fact that interference light is detected when the optical path lengths of the measurement light, reflected light, and reference light match. That is, in this method, the low-coherence light emitted from the light source is divided into measurement light and reference light, the measurement light is irradiated onto the measurement object, and the reflected light from the measurement object is guided to the multiplexing means. On the other hand, the reference light is guided to the multiplexing means after the optical path length is changed in order to change the measurement depth in the measurement target. Then, the reflected light and the reference light are combined by the combining means, and the interference light resulting from the combination is measured by heterodyne detection or the like.

  In the OCT apparatus, by changing the optical path length of the reference light, the measurement position (measurement depth) with respect to the measurement object is changed and a tomographic image is acquired. This method is generally called TD-OCT (Time domain OCT) measurement.

  On the other hand, an optical tomographic imaging device based on SD-OCT (Spectral Domain OCT) measurement or SS-OCT (Swept source OCT) measurement is proposed as a device for acquiring tomographic images at high speed without changing the optical path length of the reference light. Has been.

  In the above-described tomographic image, it is possible to acquire a two-dimensional or three-dimensional optical tomographic image of a predetermined scanning region by repeating the measurement while slightly shifting the irradiation position.

  Such an OCT apparatus (optical tomographic imaging apparatus) is capable of observing a measurement site with high precision (resolution of about 10 μm), and an OCT probe (optical probe) is inserted into the forceps opening of the endoscope apparatus. By guiding the signal light and the reflected light of the signal light and acquiring the optical tomographic image in the body cavity, for example, it is possible to diagnose the depth of invasion of the initial cancer.

In the conventional OCT apparatus, since the OCT probe has a substantially cylindrical shape, it is difficult to observe the living body tissue with a certain distance. In other words, the outer surface of the sheath can be observed while being applied to the surface of the living tissue, but it is difficult to observe it by holding it at a position farther from the surface of the living tissue than that state. In view of this, a technique has been proposed in which an optical probe can be positioned and observed at a certain distance from a living tissue (Patent Document 2).
JP-A-6-165784 JP 2002-263055 A

  However, when scanning is performed by pressing the tip of the optical probe against the measurement target site in the body cavity, for example, when the measurement target site is the side wall of the large intestine, observation is performed to invade the shape of the pit pattern (mucosal microstructure) of the large intestine. It becomes difficult. On the other hand, when observing the optical probe positioned at a certain distance from the side wall of the large intestine, the positional relationship between the optical probe and the surface of the large intestine side wall is free at a certain distance, making stable observation difficult due to the fold shape of the large intestine and peristaltic movement. In addition, a structure that can keep the optical probe and the surface of the large intestine side wall in a stable positional relationship while stretching the folds of the large intestine is required.

The present invention has been made in view of such circumstances, and maintains an optical probe and a body cavity tissue surface in a stable positional relationship and optimally observes a pit pattern (mucosal microstructure) in the body cavity tissue. It is an object of the present invention to provide an optical probe device that can be used and an operating method thereof.

In order to achieve the above object, an optical probe device according to one aspect of the present invention is provided on the distal side surface of an elongated, substantially cylindrical probe insertion portion, and uses measurement light as a measurement target for a hollow organ in a body cavity. An optical probe having an optical aperture that irradiates and receives the reflected light of the measurement light from the measurement object, and the light at a position closer to the distal end than the optical aperture and to a position proximal to the optical aperture A pleat extension means for maintaining a gap between the opening and the tissue surface of the luminal organ and extending a fold structure on the tissue surface is provided.

According to this, the pleat-stretching means is provided at a position on the distal end side from the light opening and a position on the proximal end side from the light opening, and a gap between the light opening and the tissue surface of the luminal organ. In addition to maintaining the pleat structure on the tissue surface, the optical probe and the body cavity tissue surface can be kept in a stable positional relationship, and the pit pattern (mucosal microstructure) in the body cavity tissue can be optimally observed. .

In order to achieve the above object, an optical probe device according to another aspect of the present invention is provided on the distal end side surface of an elongated, substantially cylindrical probe insertion portion, and uses measurement light as a measurement target for a hollow organ in a body cavity. Irradiate and image the inside of a body cavity having an optical probe having an optical aperture for receiving the reflected light of the measurement light from the measurement object and a treatment instrument channel through which the optical probe is inserted inside the endoscope insertion portion Maintaining a gap between the optical opening and the tissue surface of the luminal organ at the distal end of the endoscope, the probe insertion portion on the distal side of the optical opening, and the endoscope insertion portion, and the tissue And pleat extension means for extending the surface fold structure.

According to this, the pleat extension means is provided at the distal end of the probe insertion portion and the endoscope insertion portion on the distal end side from the optical opening, and the optical opening and the tissue surface of the luminal organ By maintaining the gap and stretching the pleat structure on the tissue surface, the optical probe and the body cavity tissue surface can be maintained in a stable positional relationship, and the pit pattern (mucosal microstructure) in the body cavity tissue can be optimally observed. it can.

In the optical probe device, it is preferable that the pleat extension means includes a first tip balloon provided at a tip side position of the tip side surface located on a tip side of the light opening, and a tip side position of the first side surface. A second tip balloon provided at a tip position of the second side surface of the tip side surface facing the radial direction of the probe insertion portion, tip balloon inflation means for inflating the first tip balloon and the second tip balloon, A first proximal balloon provided at a first side proximal end position on the first side side distal end position on the proximal side from the light opening and on the first side distal end position side; and the first side surface base A second proximal balloon provided at a proximal end position of the second side surface of the side surface of the probe insertion portion opposed to the end position in the radial direction of the probe insertion portion, the first proximal balloon and the second proximal balloon; Swelling And proximal balloon inflation means for, it is possible to configure the first proximal balloon and the second proximal balloon from a balloon moving means for moving the longitudinal axis direction of the probe insertion portions.

In the optical probe device, it is preferable that the pleat extension means includes a first tip balloon provided at a tip side position of the tip side surface located on a tip side of the light opening, and a tip side position of the first side surface. A second tip balloon provided at a tip position of the second side surface of the tip side surface facing the radial direction of the probe insertion portion, tip balloon inflation means for inflating the first tip balloon and the second tip balloon, A first proximal balloon provided on a first side proximal position on a distal side of the endoscope insertion portion on the first side distal position side, the first side proximal position and the endoscope insertion; A proximal end for inflating the first proximal balloon and the second proximal balloon, a second proximal balloon provided at a second lateral proximal position on the side surface of the endoscope insertion portion facing in the radial direction of the portion; Balloon inflation means; It is possible to configure the serial first proximal balloon and the second proximal balloon from a balloon moving means for moving the longitudinal axis direction of the probe insertion portion during insertion into the treatment instrument channel.

In the optical probe device, it is preferable that the optical probe apparatus includes a movement restricting unit that restricts movement of the first proximal balloon and the second proximal balloon by the balloon moving unit.

In the optical probe device, each of the first distal balloon, the second distal balloon, the first proximal balloon, and the second proximal balloon is preferably made of natural rubber.

In the optical probe device, preferably , a distal-side inflation control means for controlling the inflation of the first distal balloon and the second distal balloon by the distal balloon inflation means, and the first proximal balloon by the proximal balloon inflation means And a proximal-side inflation control means for controlling the inflation of the second proximal balloon, and a movement control means for controlling the movement of the first proximal balloon and the second proximal balloon by the balloon moving means. Can be provided.

In the optical probe device, preferably , the distal end side inflation control means and the proximal end side inflation control means control the distal balloon inflation means and the proximal balloon inflation means, and the first distal balloon and the second distal end are controlled. Each of the balloon, the first proximal balloon, and the second proximal balloon may be inflated and brought into contact with the inner wall of the luminal organ.

In the optical probe device, it is preferable that the distal side inflation control means controls the distal balloon inflation means to inflate one of the first distal balloon and the second distal balloon to be larger than the other, and the luminal organ. The proximal end side inflation control means controls the proximal end balloon inflation means, and the first distal end balloon or the second distal end balloon, which is further inflated by the distal end side inflation control means, One of the first proximal balloon and the second proximal balloon on the arranged side can be inflated larger than the other and brought into contact with the inner wall of the luminal organ.

In the optical probe device, preferably, the movement control means controls the balloon moving means after inflation control of the first distal balloon and the second distal balloon by the distal side inflation control means to control the first proximal balloon and The second proximal balloon is moved in the longitudinal axis direction of the probe insertion portion, and after the movement control, the proximal inflation control means controls the proximal balloon inflation means to control the first proximal balloon and the first balloon. The two proximal balloons can be configured to be inflated.

In the optical probe device, it is preferable that the movement control unit controls the balloon moving unit after the base end side inflation control unit controls the expansion of the first base end balloon and the second base end balloon to control the first base end balloon. The end balloon and the second proximal balloon may be configured to move in the proximal direction of the longitudinal axis of the probe insertion portion.

To achieve the above object, a method of operating an optical probe device according to another aspect of the present invention, there is provided a method of operating an optical probe device according to the above, and the first distal balloon by the distal balloon inflation means A distal-side inflation control step for controlling inflation of the second distal balloon; a proximal-side inflation control step for controlling inflation of the first proximal balloon and the second proximal balloon by the proximal balloon inflation means; A movement control step for controlling movement of the first proximal balloon and the second proximal balloon by the balloon moving means.

In the method of operating the optical probe device, preferably, the distal end side inflation control step controls inflation of the first distal end balloon and the second distal end balloon, and the proximal end side inflation control step performs the first proximal end. By controlling the inflation of the balloon and the second proximal balloon and controlling the movement of the first proximal balloon and the second proximal balloon in the movement control step, the optical probe and the body cavity tissue surface are stabilized. The pit pattern (mucosal microstructure) in the body cavity tissue can be optimally observed while maintaining the above positional relationship.

In the operating method of the optical probe device, preferably, the movement control step controls the balloon moving means after the inflation control of the first tip balloon and the second tip balloon by the tip side inflation control step to control the first group. The proximal balloon and the second proximal balloon are moved in the longitudinal axis direction of the insertion portion, and after the movement control, the proximal inflation control step controls the proximal balloon inflation means to control the first proximal balloon and the second balloon. The second proximal balloon can be configured to be inflated.

In the operation method of the optical probe device, preferably, the movement control step controls the balloon moving means after the inflation control of the first proximal balloon and the second proximal balloon by the proximal inflation control step to control the balloon moving means. The first proximal balloon and the second proximal balloon can be configured to move in the proximal direction of the longitudinal axis of the insertion portion.

In the operation method of the optical probe device, preferably, the distal side inflation control step and the proximal side inflation control step control the distal balloon inflation means and the proximal balloon inflation means, and the first distal balloon, Each of the second distal balloon, the first proximal balloon and the second proximal balloon can be inflated and brought into contact with the inner wall of the luminal organ.

In the operation method of the optical probe device, preferably, the distal end side inflation control step causes the distal end balloon inflating means to inflate one of the first distal end balloon and the second distal end balloon to be larger than the other, and The proximal-side inflation control step is brought into contact with the inner wall, and the proximal-side inflation control step includes the first proximal-end balloon on the side where the first distal-end balloon or the second distal-end balloon is disposed, One of the second proximal balloons can be inflated larger than the other and brought into contact with the inner wall of the luminal organ.

In the operating method of the optical probe device, preferably, the movement control step includes the first proximal balloon and the first proximal balloon and the second distal balloon by the balloon moving means after the inflation control of the first distal balloon and the second distal balloon by the distal inflation control step. The second proximal balloon is moved in the longitudinal axis direction of the probe insertion portion, and after the movement control, the proximal-side inflation control step is performed by the proximal balloon inflation means by the first balloon balloon and the second proximal balloon. The balloon can be configured to be inflated.

In the operation method of the optical probe device, preferably, the movement control step is performed by the balloon moving unit after the first base end balloon and the second base end balloon are inflated by the base end side inflation control unit. The end balloon and the second proximal balloon may be configured to move in the proximal direction of the longitudinal axis of the probe insertion portion.

  As described above, according to the present invention, the optical probe and the body cavity tissue surface are maintained in a stable positional relationship, and the pit pattern (mucosal microstructure) in the body cavity tissue can be optimally observed. is there.

  The best mode for carrying out the present invention will be described below with reference to the accompanying drawings.

First embodiment:
FIG. 1 is an example of an external view showing an image diagnostic apparatus 10 according to the first embodiment. As shown in FIG. 1, an image diagnostic apparatus 10 as an optical probe apparatus according to the present embodiment mainly includes an endoscope 100, an endoscope processor 200, a light source device 300, an OCT processor 400, and a monitor device 500. ing. The endoscope processor 200 may be configured to incorporate the light source device 300.

  The endoscope 100 includes a hand operation unit 112 and an insertion unit 114 that is connected to the hand operation unit 112. The surgeon grasps and operates the hand operation unit 112 and performs observation by inserting the insertion unit 114 into the body of the subject.

  A universal cable 116 is connected to the hand operation unit 112, and an LG connector 120 is provided at the tip of the universal cable 116. By connecting the LG connector 120 to the light source device 300 in a detachable manner, illumination light is sent to the illumination optical system 152 disposed at the distal end portion of the insertion portion 114. The LG connector 120 is connected to an electrical connector 110 via a universal cable 116, and the electrical connector 110 is detachably coupled to the endoscope processor 200. As a result, observation image data obtained by the endoscope 100 is output to the endoscope processor 200 and an image is displayed on the monitor device 500 connected to the endoscope processor 200.

  The hand operating unit 112 is provided with an air / water feed button 126, a suction button 128, a shutter button 130, a function switching button 132, a pair of angle knobs 134, and a pair of lock levers 136. The description about is omitted.

  Further, the hand operation section 112 is provided with a forceps insertion portion 138, and the forceps insertion portion 138 is communicated with the forceps port 156 of the distal end portion 144. In the diagnostic imaging apparatus 10 according to the present embodiment, the OCT probe 600 as an optical probe is inserted from the forceps insertion portion 138, whereby the OCT probe 600 is led out from the forceps port 156.

  The OCT probe 600 is inserted from the forceps insertion part 138 and inserted from the forceps port 156, an operation part 604 for the operator to operate the OCT probe 600, and the OCT processor 400 via the connector 410. It consists of a cable 606 to be connected.

  On the other hand, the insertion portion 114 of the endoscope 100 includes a flexible portion 140, a bending portion 142, and a distal end portion 144 in this order from the hand operating portion 112 side. The distal end portion 144 is provided with an observation optical system 150, an illumination optical system 152, an air / water supply nozzle 154, a forceps port 156, and the like. A description of the air / water supply nozzle 154 is omitted.

  The observation optical system 150 is disposed on the distal end surface of the distal end portion 144, and a CCD 140, which will be described later, which is a solid-state imaging device, is disposed behind the observation optical system 150. A signal cable (not shown) is connected to the substrate of the CCD 140, and this signal cable is inserted into the insertion portion 114, the hand operating portion 112, the universal cable 116, and the like and extended to the electrical connector 110, and the endoscope processor 200. Connected to. Therefore, the observation image captured by the observation optical system 150 is formed on the light receiving surface of the CCD 140 and converted into an electric signal, and this electric signal is output to the endoscope processor 200 and converted into a video signal. Thereby, an observation image is displayed on the monitor device 500 connected to the endoscope processor 200.

  The illumination optical system 152 is provided adjacent to the observation optical system 150, and is disposed on both sides of the observation optical system 150 as necessary. An exit end of a light guide (not shown) is disposed in the back of the illumination optical system 152. This light guide is inserted into the insertion portion 114, the hand operating portion 112, and the universal cable 116, and the incident end of the light guide is LG. Located in the connector 120. Therefore, by connecting the LG connector 120 to the light source device 300, the illumination light irradiated from the light source device 300 is transmitted to the illumination optical system 152 through the light guide, and is irradiated from the illumination optical system 152 to the front observation range. The

  A forceps channel (not shown) as a tube-like treatment instrument channel is connected to the forceps port 156. The forceps channel is inserted into the insertion portion 114 and then branched. One of the forceps channels communicates with the forceps insertion portion 138 of the hand operation portion 112 and the other is connected to a suction valve (not shown) in the hand operation portion 112. . The suction valve is operated by a suction button 128, whereby a lesioned part or the like can be sucked from the forceps opening 156.

  A bending portion 142 is provided on the proximal end side of the distal end portion 144 configured as described above. The bending portion 142 is configured to be bent remotely by rotating the angle knobs 134 and 134 of the hand operation unit 112.

  A flexible portion 140 is provided on the proximal end side of the bending portion 142. The soft part 140 has flexibility and is configured by covering a core material made of, for example, a metal net tube with a coating such as resin.

  FIG. 2 is an example of a block diagram illustrating an internal configuration of the endoscope, the endoscope processor, and the light source device of FIG.

  As shown in FIG. 2, the endoscope processor 200 mainly includes a central processing unit (CPU) 210, an analog front end (AFE) 220, an image input controller 222, an image processing unit 224, an image input interface unit 226, a position. Detection unit 228, image synthesis unit 230, CCD driver 240, timing generator (TG) 242, character generator (CG) 244, memory 246, video output unit 248, audio processing unit 250, speaker 252, operation unit 254, and communication interface Part 258.

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 controls each unit by reading a control program recorded in the program ROM into the memory 246 based on an instruction input such as a shooting instruction from the operation unit 254 and sequentially executing the control 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 endoscope 100 outputs the charge 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 254 has a keyboard, a mouse, and the like for inputting instructions for communication with the image server 700, as will be described later, in addition to a switch for instructing start and end of shooting.

  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 image processing unit 224, the image input interface unit 226, the image composition unit 230, the CG 244, the video output unit 248, the communication interface unit 258, and the like are connected to the bus 256. These are capable of transmitting and receiving information to and from each other via a bus 256.

  The image signal for one frame stored in the memory 246 is captured by the image processing unit 224 and subjected to necessary image processing.

  The endoscope processor 200 receives an image signal of a tomographic image output from the OCT processor 400 via the image input interface unit 226. This image signal is converted into a video signal for the monitor device 500 by the video output unit 248 and output to the monitor device 500.

  Further, the CG 244 generates a warning character or the like according to a command from the CPU 210 and outputs it to the image composition unit 230, and the sound processing unit 250 generates a warning sound such as a beep sound or a warning sound from the speaker 252 according to a command from the CPU 210. Let

  The image synthesizing unit 230 performs processing for superimposing a warning character or the like generated by the CG 244 on a tomographic image or an endoscopic image, thereby displaying the warning character or the like on the screen of the monitor device 500.

  The position detection unit 228 detects the position (insertion depth) of the endoscope from the output signal of the position sensor 229 provided in the endoscope 100. The position information of the endoscope is superimposed in the image composition unit 230 and displayed on the monitor device 500 together with the endoscope image and the like.

  The light source device 300 mainly includes a white light source 310, a diaphragm 330, a condenser lens 340, and an automatic light amount adjustment circuit (ALC) 370, and makes visible light incident on the light guide 170.

  As the 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 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.

  FIG. 3 is a cross-sectional view showing a cross-section of the tip of the OCT probe of FIG. 1, and FIG. 4 is a diagram showing a configuration of the side of the tip of the OCT probe of FIG.

  As shown in FIG. 3, the distal end portion of the insertion portion 602 of the OCT probe 600 has a probe outer cylinder 620, a cap 622, an optical fiber 623, a spring 624, a fixing member 626, and an optical lens 628. doing.

  The probe outer cylinder (sheath) 620 is a cylindrical member having flexibility, and a material (a part of the side surface on the distal end side through which the measurement light L1 and the reflected light L3 pass) transmits light over the entire circumference. A light aperture 650 formed of a transparent material.

  The cap 622 is provided at the distal end of the probe outer cylinder 620 and closes the distal end of the probe outer cylinder 620.

  The optical fiber 623 is a linear member, and is accommodated in the probe outer cylinder 620 along the probe outer cylinder 620. The optical lens 628 emits measurement light L1 emitted from an optical fiber FB2 described later in the OCT processor 400. And the reflected light L3 from the measuring object S acquired by the optical lens 628 is guided to the optical fiber FB2.

  Here, the optical fiber 623 and the optical fiber FB2 are connected by a rotary joint (not shown) or the like in a later-described rotation drive unit 26 provided in the operation unit 604 of the OCT probe 600, and the optical fiber 623. Is optically connected in a state where the rotation of is not transmitted to the optical fiber FB2. The optical fiber 623 is disposed so as to be rotatable with respect to the probe outer cylinder 620.

  The spring 624 is fixed to the outer periphery of the optical fiber 623. The optical fiber 623 and the spring 624 are connected to the rotation drive unit 26.

  The optical lens 628 is disposed at the tip of the optical fiber 623, and the tip is formed in a substantially spherical shape for condensing the measurement light L1 emitted from the optical fiber 623 onto the measurement object S. .

  The optical lens 628 irradiates the measurement object S with the measurement light L 1 emitted from the optical fiber 623, collects the reflected light L 3 from the measurement object S, and enters the optical fiber 623.

  The fixing member 626 is disposed on the outer periphery of the connection portion between the optical fiber 623 and the optical lens 628, and fixes the optical lens 628 to the end portion of the optical fiber 623. Here, the fixing method of the optical fiber 623 and the optical lens 628 by the fixing member 626 is not particularly limited. For example, even if the fixing member 626 is bonded to the optical fiber 623 and the optical lens 628 with an adhesive, the bolt or the like is used. May be fixed with a mechanical structure. Any fixing member 626 may be used as long as it is used for fixing, holding or protecting the optical fiber, such as a zirconia ferrule or a metal ferrule.

  The rotation drive unit 26 provided on the proximal end side of the OCT probe 600 is connected to the optical fiber 623 and the spring 624, and the optical lens 628 is moved to the probe outer cylinder by rotating the optical fiber 623 and the spring 624. 11 is rotated in the direction of arrow R2. The rotation drive unit 26 includes a rotation encoder, and detects the irradiation position of the measurement light L1 from the position information (angle information) of the optical lens 628 based on a signal from the rotation encoder. That is, the measurement position is detected by detecting the angle of the rotating optical lens 628 with respect to the reference position in the rotation direction.

  Furthermore, the optical fiber 623, the spring 624, the fixing member 626, and the optical lens 628 are moved in the direction of the arrow S <b> 1 (forceps opening direction) and the direction S <b> 2 in the probe outer cylinder 620 by an advance / retreat mechanism (not shown) of the rotation drive unit 26. It is configured to be movable in the direction of the tip of the probe outer cylinder 620.

  The OCT probe 600 is configured as described above, and the optical fiber 623 and the spring 624 are rotated in the direction of the arrow R2 in FIG. 3 by the rotation driving unit 26, so that the measurement light L1 emitted from the optical lens 628 is emitted. The measurement object S is irradiated while scanning in the direction of the arrow R2 (circumferential direction of the probe outer cylinder 620), and the return light L3 is acquired.

  A pair of a tip balloon 651 as a first tip balloon and a tip balloon 652 as a second tip balloon are provided on the side surface of the probe outer tube 620 on the tip side of the optical opening 650 of the probe outer tube 620. ing. The distal balloon 651 is made of, for example, natural rubber and is provided on the side surface of the probe outer cylinder 620 on the light opening 650 side. The distal balloon 652 is made of, for example, natural rubber, and is provided on the side surface of the probe outer cylinder 620 that faces the distal balloon 651 in the radial direction of the probe outer cylinder 620.

  On the other hand, on the side surface of the probe outer cylinder 620 on the proximal side of the optical opening 650 of the probe outer cylinder 620, a proximal balloon 653 as a pair of first proximal balloons and a proximal end as a second proximal balloon are provided. A balloon 654 is provided. The proximal balloon 653 is made of, for example, natural rubber and is provided on the side surface of the probe outer cylinder 620 on the light opening 650 side. The proximal balloon 654 is made of natural rubber, for example, and is provided on the side surface of the probe outer cylinder 620 that faces the distal balloon 651 in the radial direction of the probe outer cylinder 620.

  The pair of proximal balloons 653 and 654 are fixed to a moving member 655 that can advance and retract the probe outer cylinder 620 in the longitudinal axis direction. For example, a flexible rod member 656 connected to the OCT processor 400 is used. By moving the moving member 655 forward and backward, the proximal balloons 653 and 654 advance and retract in the longitudinal axis direction of the probe outer cylinder 620. Note that the base end of the bar member 656 is connected to an advance / retreat drive unit 671 (see FIG. 6, described later) of the OCT processor 400 as described later.

  The balloon moving means includes a moving member 655, a bar member 656, and an advance / retreat drive unit 671.

  The moving member 655 is provided inside the probe outer cylinder 620, and is advanced and retracted by a plurality of restricting members 657 that are embedded in the outer cylinder wall and movable in the radial direction. ing. More specifically, each regulating member 657 is for resisting the reaction force of the folds that have been stretched or stretched. When the moving member 655 is moved by the bar member 656, the range of the moving member 655 is not limited. When the movable member 655 sinks into the outer cylinder wall and protrudes from the outer cylinder wall in the range in which the movable member 655 moves, the protruding regulating member 657 does not act on the movable member 655 by the bar member 656, so that the movable member 655 The probe outer cylinder 620 is configured to be restricted from moving in the distal direction of the longitudinal axis.

  The distal balloons 651 and 652 and the proximal balloons 653 and 654, the moving member 655, the rod member 656, the regulating member 657, the advancing / retreating driving unit 671, and the air / intake unit 672 constitute pleat stretching means.

  As shown in FIG. 4, the distal balloons 651 and 652 and the proximal balloons 653 and 654 are arranged on the side surface of the probe outer cylinder 620 along the longitudinal axis of the probe outer cylinder 620. , 662, 663, 664. The distal balloons 651 and 652 and the proximal balloons 653 and 654 perform air supply / intake independently through these air supply / intake pipelines 661, 662, 663, and 664, respectively. It is possible to expand and contract to the volume of. Note that the base ends of the air supply / intake pipelines 661, 662, 663, and 664 are connected to an air supply / intake unit 672 (see FIG. 6, described later) of the OCT processor 400, as will be described later.

  The distal balloon inflating means and the proximal balloon inflating means are constituted by an air supply / intake unit 672.

  FIG. 5 is an example of a diagram illustrating a state in which a tomographic image is obtained using an OCT probe derived from the forceps opening of the endoscope of FIG. As shown in the figure, the OCT processor 400 obtains a tomographic image by bringing the distal end portion of the insertion portion 602 of the OCT probe 600 close to a desired portion of the measurement target S.

  FIG. 6 is an example of a block diagram showing the internal configuration of the OCT processor of FIG. As shown in FIG. 6, the OCT processor 400 divides the light emitted from the light source unit 12 and the light emitted from the light source unit 12 into measurement light and reference light, and combines the reflected light and reference light. A branching / multiplexing unit 14 that generates interference light, an optical path length adjusting unit 18 that adjusts the optical path length of the reference light, and an interference light detection unit 20 that detects the interference light generated by the branching / multiplexing unit 14 as an interference signal. And a processing unit 22 that processes the interference signal detected by the interference light detection unit 20. Further, the OCT processor 400 includes various conditions for the optical fiber coupler 28 that splits the light emitted from the light source unit 12, the detection unit 30a that detects the reference light, the detection unit 30b that detects the reflected light, and the processing unit 22. And an operation control unit 32 for changing settings and the like. Further, an optical fiber is used as a light path, and measurement light, reference light, reflected light, and the like are guided to each part.

  The light source unit 12 includes a semiconductor optical amplifier 40, an optical splitter 42, a collimator lens 44, a diffraction grating element 46, an optical system 48, and a rotary polygon mirror 50, and sweeps the frequency at a constant period. The laser beam La is emitted to the optical fiber FB10.

  The optical splitter 42 is provided on the optical path of the optical fiber FB10 and is also connected to the optical fiber FB11. The optical branching device 42 branches a part of the light guided in the optical fiber FB10 to the optical fiber FB11.

  The collimator lens 44 is disposed at the other end of the optical fiber FB11, that is, the end not connected to the optical fiber FB10, and makes the light emitted from the optical fiber FB11 parallel light.

  The diffraction grating element 46 is disposed at a predetermined angle on the optical path of the parallel light generated by the collimator lens 44. The diffraction grating element 46 splits the parallel light emitted from the collimator lens 44.

  The optical system 48 is disposed on the optical path of the light split by the diffraction grating element 46. The optical system 48 is composed of a plurality of lenses, refracts the light split by the diffraction grating element 46, and converts the refracted light into parallel light.

  The rotating polygon mirror 50 is disposed on the optical path of the parallel light generated by the optical system 48 and reflects the parallel light. The rotating polygon mirror 50 is a rotating body that rotates at a constant speed in the R1 direction in FIG. 6. The surface perpendicular to the rotation axis is a regular octagon, and the side surface (each side of the octagon is irradiated with parallel light). Surface) is formed of a reflecting surface that reflects the irradiated light. The rotating polygon mirror 50 rotates to change the angle of each reflecting surface with respect to the optical axis of the optical system 48.

  The light emitted from the optical fiber FB11 passes through the collimator lens 44, the diffraction grating element 46, and the optical system 48, and is reflected by the rotary polygon mirror 50. The reflected light passes through the optical system 48, the diffraction grating element 46, and the collimator lens 44 and enters the optical fiber FB11.

  Here, as described above, since the angle of the reflecting surface of the rotating polygon mirror 50 changes with respect to the optical axis of the optical system 48, the angle at which the rotating polygon mirror 50 reflects light changes with time. For this reason, only the light in a specific frequency region out of the light dispersed by the diffraction grating element 46 is incident on the optical fiber FB11 again. Here, since the light in a specific frequency range incident on the optical fiber FB11 is determined by the angle between the optical axis of the optical system 48 and the reflection surface of the rotary polygon mirror 50, the frequency range of the light incident on the optical fiber FB11 is It changes depending on the angle between the optical axis of the optical system 48 and the reflecting surface of the rotary polygon mirror 50.

  The light in a specific frequency range that has entered the optical fiber FB11 is incident on the optical fiber FB10 from the optical splitter 42, and is combined with the light in the optical fiber FB10. Thereby, the pulsed laser light guided to the optical fiber FB10 becomes laser light in a specific frequency range, and the laser light La in the specific frequency range is emitted to the optical fiber FB1.

  Here, since the rotary polygon mirror 50 rotates at a constant speed in the direction of the arrow Rl, the wavelength λ of the light incident on the optical fiber FB1l again changes with a constant period as time passes. As a result, the frequency of the laser light La emitted to the optical fiber FB1 also changes at a constant period with the passage of time.

  The light source unit 12 has such a configuration, and emits the laser light La swept in wavelength toward the optical fiber FB1.

  Next, the branching / combining unit 14 is configured by, for example, a 2 × 2 optical fiber coupler, and is optically connected to the optical fiber FB1, the optical fiber FB2, the optical fiber FB3, and the optical fiber FB4, respectively.

  The branching / combining unit 14 divides the light La incident from the light source unit 12 through the optical fiber FB1 into the measurement light L1 and the reference light L2, causes the measurement light L1 to enter the optical fiber FB2, and the reference light L2 The light is incident on the fiber FB3. The optical fiber 623 of the OCT probe 600 and the optical fiber FB2 are connected by a rotary joint (not shown) in the rotation drive unit 26 provided on the proximal end side of the OCT probe 600, and the like. The optical connection is made in a state where the rotation is not transmitted to the optical fiber FB2. Therefore, the measurement light L1 is guided to the optical fiber 623 of the OCT probe 600 via the optical fiber FB2, and the reflected light L3 from the measurement object S is guided to the optical fiber FB2 via the optical fiber 623 of the OCT probe 600. Waved.

  Further, the reference light L2 enters the optical fiber FB3, and after the frequency shift and the optical path length are changed by the optical path length adjusting unit 18 described later, the reference light L2 returns through the optical fiber FB3. Then, the reference light L2 incident on the branching / combining unit 14 is combined with the reflected light L3 from the measurement target S acquired by the OCT probe 600 and incident on the branching / combining unit 14 from the optical fiber FB2, and is combined with the optical fiber FB4. Eject.

  The optical path length adjusting unit 18 is arranged on the reference light L2 emission side of the optical fiber FB3 (that is, the end of the optical fiber FB3 opposite to the branching / combining unit 14).

  The optical path length adjustment unit 18 includes a first optical lens 64 that converts the light emitted from the optical fiber FB3 into parallel light, a second optical lens 66 that condenses the light converted into parallel light by the first optical lens 64, and A reflection mirror 68 that reflects the light collected by the second optical lens 66, a base 70 that supports the second optical lens 66 and the reflection mirror 68, and the base 70 are moved in a direction parallel to the optical axis direction. The optical path length of the reference light L2 is adjusted by changing the distance between the first optical lens 64 and the second optical lens 66.

  The first optical lens 64 converts the reference light L2 emitted from the core of the optical fiber FB3 into parallel light, and condenses the reference light L2 reflected by the reflection mirror 68 on the core of the optical fiber FB3.

  The second optical lens 66 condenses the reference light L2 made parallel by the first optical lens 64 on the reflection mirror 68, and makes the reference light L2 reflected by the reflection mirror 68 parallel. Thus, the first optical lens 64 and the second optical lens 66 form a confocal optical system.

  The reflection mirror 68 is disposed at the focal point of the light collected by the second optical lens 66 and reflects the reference light L2 collected by the second optical lens 66.

  As a result, the reference light L2 emitted from the optical fiber FB3 becomes parallel light by the first optical lens 64 and is condensed on the reflection mirror 68 by the second optical lens 66. Thereafter, the reference light L2 reflected by the reflecting mirror 68 becomes parallel light by the second optical lens 66, and is condensed on the core of the optical fiber FB3 by the first optical lens 64.

  The base 70 fixes the second optical lens 66 and the reflection mirror 68, and the mirror moving mechanism 72 moves the base 70 in the optical axis direction of the first optical lens 64 (direction of arrow A in FIG. 4). . The distance between the first optical lens 64 and the second optical lens 66 can be changed by moving the base 70 in the arrow A direction by the mirror moving mechanism 72, and the optical path length of the reference light L2 can be adjusted. Can do.

  The interference light detection unit 20 is connected to the optical fiber FB4, and detects the interference light L4 generated by combining the reference light L2 and the reflected light L3 by the branching / combining unit 14 as an interference signal.

  Here, the OCT processor 400 is provided in the optical fiber coupler 28 that branches the laser light La from the optical fiber FB1 to the optical fiber FB5, and the optical fiber FB5 that branches off from the optical fiber coupler 28. It has the detection part 30a which detects light intensity, and the detection part 30b which detects the light intensity of the interference light L4 on the optical path of optical fiber FB4. The interference light detection unit 20 adjusts the balance of the light intensity of the interference light L4 detected from the optical fiber FB4 based on the detection results of the detection unit 30a and the detection unit 30b.

  The processing unit 22 detects the measurement region of the OCT probe 600 at the measurement position from the interference signal detected by the interference light detection unit 20, and further acquires a tomographic image from the interference signal detected by the interference light detection unit 20.

  The operation control unit 32 includes input means such as a keyboard and a mouse, and control means for managing various conditions based on the input information, and is connected to the processing unit 22. The operation control unit 32 inputs, sets, and changes various processing conditions in the processing unit 22 based on an operator's instruction input from the input unit.

  Further, the operation control unit 32 is configured so that the advance / retreat drive unit 671 for connecting the proximal end of the bar member 656 and the air supply / intake pipes 661, 662, 663, 664 are based on the operator's instruction input from the input means. The air supply / intake unit 672 connecting the base ends is controlled.

  The distal end side expansion control means, the proximal end side expansion control means, and the movement control means are configured by the operation control unit 32.

  Note that the operation control unit 32 may display the operation screen on the monitor device 500, or may provide a separate display unit to display the operation screen. Further, the operation control unit 32 may be configured to perform operation control of the light source unit 12, the rotation driving unit 26, the interference light detection unit 20, the optical path length, the detection units 30a and 30b, and setting of various conditions.

  The OCT processor 400 described above uses an SS-OCT (Swept source OCT) measurement method. However, the OCT measurement method is not limited to this, and TD-OCT (Time domain OCT) measurement or SD-OCT is used as the OCT measurement method. (Spectral Domain OCT) measurement method may be used.

  The operation of the present embodiment configured as described above will be described with reference to the flowchart of FIG. FIG. 7 is a flowchart for explaining the operation of the diagnostic imaging apparatus shown in FIG.

  As shown in FIG. 7, when the operator turns on the power and the endoscope 100 is inserted into the body cavity, the diagnostic imaging apparatus 10 starts an endoscopic examination by the endoscope processor 200 (step S1). .

  Then, the diagnostic imaging apparatus 10 determines whether or not an instruction to perform OCT measurement is given by the operator during the endoscopic examination (step S2). An instruction to perform OCT measurement is given by the operation control unit 32 of the OCT processor 400 in order for the operator to acquire an optical tomographic image of the affected area.

  When an instruction to perform OCT measurement is made, the diagnostic imaging apparatus 10 allows the surgeon to insert the OCT probe 600 from the forceps insertion portion 138 of the endoscope 100 and the distal end of the OCT probe 600 from the forceps port 156 via the forceps channel. And waits for a completion instruction from the operation control unit 32 of the approach of the tip of the OCT probe 600 to the measuring object S in the body cavity (step S3). When this completion instruction is input, the diagnostic imaging apparatus 10 instructs the operation control unit 32 of the OCT processor 400 to start balloon control.

  8 to 11 are diagrams for explaining balloon control in a narrow organ duct in which the insertion part of the endoscope is difficult to insert in the process of FIG.

  In the following balloon control, as shown in FIG. 8, for example, the insertion portion 114 (see FIG. 1) of the endoscope 100 is difficult to insert, and only the OCT probe 600 can be inserted, for example, a duct such as a bile duct or pancreatic duct A narrow organ duct 800 will be described as an example.

  In such a narrow organ duct OCT probe 600 approach, the operator inserts the insertion portion 114 of the endoscope 100 into the duodenum, and inserts the OCT probe 600 protruding from the forceps opening 156 into the bile duct or pancreatic duct, For example, it is performed by bringing the optical aperture 650 closer to the measurement object S based on an X-ray CT image captured in advance.

  In this balloon control, the operation control unit 32 first controls the air supply / inhalation unit 672 to inflate the distal balloon 651 so as to maintain a predetermined distance from the inner wall of the organ duct 800 as shown in FIG. The tip balloon 652 is inflated to substantially the same volume as the tip balloon 651 and the tip balloon 652 is brought into contact with the inner wall of the organ duct 800 (step S4).

  Then, the operation control unit 32 controls the advance / retreat drive unit 671 and drives the rod member 656 to move the moving member 655 forward and backward by a predetermined amount ΔD (see FIG. 9) in the longitudinal axis direction of the OCT probe 600. The balloons 653 and 654 are positioned (step S5). This positioning is determined by, for example, the shape / size of the folds in the organ duct 800 around the measurement target S based on an X-ray CT image captured in advance. The position of the positioned moving member 655 is held by the regulating member 657.

  When the positioning is completed, the operation control unit 32 controls the insufflation / inhalation unit 672 to inflate the proximal balloon 653 so as to maintain a predetermined distance from the inner wall of the organ duct 800 as shown in FIG. The proximal balloon 654 is inflated to substantially the same volume as the proximal balloon 653, and the proximal balloon 654 is brought into contact with the inner wall of the organ duct 800 (step S6).

  Next, as shown in FIG. 11, the operation control unit 32 controls the advance / retreat drive unit 671 to drive the rod member 656 in a state where the proximal balloons 653 and 654 are in contact with the inner wall of the organ duct 800. As a result, the moving member 655 is further moved by a predetermined amount δd toward the proximal end of the longitudinal axis of the OCT probe 600, and the folds in the organ duct 800 are extended (step S7). The predetermined amount δd that moves in the proximal direction of the longitudinal axis is determined by, for example, the shape / size and position of the fold in the organ duct 800 around the measurement target S based on an X-ray CT image captured in advance. The position of the moving member 655 that has moved by a predetermined amount ΔD + δd in the proximal direction of the longitudinal axis is held by the restricting member 657.

  When the balloon control by the operation control unit 32 is completed in this way, the operation control unit 32 controls each unit of the OCT processor 400, starts OCT measurement, acquires an optical tomographic image of the measurement target S (step S8), The optical tomographic image is displayed on the monitor device 500 (step S9).

  And the process of the said step S2-step S9 is repeated until an endoscopy is complete | finished (step S10).

  Note that the positions of the proximal balloons 653 and 654 may be determined from the beginning based on the shape / size and position of the folds, and the distal balloons 651 and 652 and the proximal balloons 653 and 654 may be inflated simultaneously.

  As described above, in the present embodiment, the distal balloon 651 is inflated so as to maintain a predetermined distance from the inner wall of the organ duct 800 and is brought into contact with the inner wall, and the distal balloon 652 is inflated so that the distal balloon 652 is brought into contact with the organ duct 800. The proximal balloon 653 is further inflated so as to maintain a predetermined distance from the inner wall of the organ duct 800 to be in contact with the inner wall, and the proximal balloon 654 is inflated to cause the proximal balloon 654 to be in contact with the organ. Since it is brought into contact with the inner wall of the duct 800, the OCT probe 600 (the optical opening 650 thereof) and the body cavity tissue surface of the organ duct 800 can be kept in a stable positional relationship.

  Further, in the present embodiment, the advancing / retreating drive unit 671 is controlled in a state where the proximal balloons 653 and 654 are in contact with the inner wall of the organ duct 800, and the rod member 656 is driven, thereby moving the moving member 655 to the OCT probe. Since the pleat in the organ duct 800 is extended by a predetermined amount in the proximal direction of the longitudinal axis 600, the pit pattern (mucosal microstructure) in the body cavity tissue of the organ duct 800 is optimally observed.

(Modification)
FIG. 12 is a view for explaining a modified example of balloon control in a wide organ duct into which the insertion portion of the endoscope can be inserted in the processing of FIG.

  In the first embodiment, the endoscope 100 is difficult to insert and only the OCT probe 600 can be inserted. For example, the organ duct 800 having a narrow duct such as the bile duct or pancreatic duct has been described. As shown, in the case of an organ duct 801 such as a large intestine where the insertion section 114 of the endoscope 100 can be inserted, the operation control section 32 controls the air supply / intake section 672 in step S4. The distal balloon 651 is inflated so as to maintain a predetermined distance from the inner wall of the organ duct 800 and is brought into contact with the inner wall, and the distal balloon 652 is inflated to a volume larger than the distal balloon 651, so that the distal balloon 652 is expanded into the organ duct. It abuts on the inner wall of the path 800.

  Further, after the positioning in step S5, the operation control unit 32 controls the air supply / inhalation unit 672 in step S6, and inflates the proximal balloon 653 so as to maintain a predetermined distance from the inner wall of the organ duct 800, thereby causing the inner wall to expand. The proximal balloon 654 is inflated to a larger volume than the proximal balloon 653, and the proximal balloon 654 is brought into contact with the inner wall of the organ duct 800.

  Further, in step S7, the operation control unit 32 controls the advance / retreat driving unit 671 and moves the rod member 656 by driving the rod member 656 with the proximal balloons 653 and 654 in contact with the inner wall of the organ duct 800. The member 655 is further moved by a predetermined amount δd in the direction of the proximal end of the longitudinal axis of the OCT probe 600, and the fold in the organ duct 800 is extended. Other operations are the same as those in the first embodiment.

  Even in the case of an organ duct 801 such as the large intestine, the similar action and effect can be obtained by inflating the distal balloon 652 to a larger volume than the distal balloon 651 and inflating the proximal balloon 654 to a larger volume than the proximal balloon 653. Can be obtained.

Second embodiment:
Since the second embodiment is almost the same as the first embodiment, only different configurations will be described, the same reference numerals are given to the same configurations, and descriptions thereof will be omitted.

  FIG. 13 is a view showing a proximal balloon provided at the distal end of the insertion portion of the endoscope according to the second embodiment, and FIG. 14 is an air supply / intake portion and a movement for inflating / deflating the proximal balloon of FIG. It is a figure which shows the arrangement structure of the advancing / retreating drive part which moves a member.

  In the present embodiment, as shown in FIG. 13, the proximal balloons 653 and 654, the moving member 655, and the regulating member 657 are configured to be disposed at the distal end portion 144 of the insertion portion 114 of the endoscope 100.

  In the present embodiment, as shown in FIG. 14, the advance / retreat drive unit 671 and the air supply / intake unit 672 are provided in the endoscope processor 200 and controlled by the CPU 210 via the bus 256. In the present embodiment, the movement control means and the proximal end side expansion control means are configured by the CPU 210. Other configurations are the same as those of the first embodiment.

  In the present embodiment, as described in the modification of the first embodiment, in the case of an organ conduit 801 such as a large intestine where the endoscope 100 can be inserted, the operation control unit 32 7, the air supply / inhalation unit 672 is controlled to inflate the distal balloon 651 with the inner wall of the organ duct 801 so as to maintain a predetermined distance and contact the inner wall with the distal balloon 652. The volume is expanded to a volume larger than 651, and the distal balloon 652 is brought into contact with the inner wall of the organ duct 801.

  Further, after the positioning in step S5 in FIG. 7, the operation control unit 32 controls the insufflation / inhalation unit 672 in step S6 in FIG. 7, and keeps the proximal balloon 653 at a predetermined distance from the inner wall of the organ duct 801. The proximal balloon 654 is inflated so that the proximal balloon 654 is brought into contact with the inner wall of the organ duct 801.

  Furthermore, the operation control unit 32 controls the advance / retreat drive unit 671 to drive the rod member 656 in a state where the proximal balloons 653 and 654 are in contact with the inner wall of the organ duct 801 in step S7 of FIG. As a result, the moving member 655 is further moved by a predetermined amount δd in the proximal end direction of the longitudinal axis of the insertion portion 114 of the endoscope 100, and the fold in the organ duct 801 is extended. Other operations are the same as those in the first embodiment.

  As described above, in the present embodiment as well, in the case of the organ duct 801 such as the large intestine, the distal balloon 652 provided on the OCT probe 600 is inflated and the endoscope 100, as in the modification of the first embodiment. In a state where the proximal balloon 654 provided at the distal end 144 of the insertion portion 114 is inflated and the proximal balloons 653 and 654 are in contact with the inner wall of the organ duct 801, the advance / retreat driving unit 671 is controlled to By driving the member 656, the moving member 655 is moved by a predetermined amount in the proximal direction of the longitudinal axis of the insertion portion 114 of the endoscope 100, and the folds in the organ duct 800 are extended, so that the same as in the first embodiment. Actions and effects can be obtained.

  As described above, the diagnostic imaging apparatus which is the optical probe apparatus of the present invention has been described in detail. However, the present invention is not limited to the above examples, and various improvements and modifications are made without departing from the gist of the present invention. Of course.

1 is an external view showing a diagnostic imaging apparatus 10 according to a first embodiment. The block diagram which shows the internal structure of the endoscope of FIG. 1, an endoscope processor, and a light source device. Sectional drawing which shows the front-end | tip cross section of the OCT probe of FIG. The figure which shows the structure of the front end side of the OCT probe of FIG. The figure which shows a mode that a tomographic image is acquired using the OCT probe derived | led-out from the forceps opening | mouth of the endoscope of FIG. The block diagram which shows the internal structure of the OCT processor of FIG. Flowchart for explaining the operation of the image diagnostic apparatus of FIG. FIG. 7 is a first diagram for explaining balloon control in a narrow organ duct where insertion of the endoscope is difficult to insert in the processing of FIG. FIG. 7 is a second diagram for explaining balloon control in a narrow organ duct where insertion of the endoscope is difficult to insert in the processing of FIG. FIG. 7 is a third diagram for explaining balloon control in a narrow organ duct where insertion of the endoscope is difficult to insert in the processing of FIG. FIG. 8 is a fourth diagram for explaining balloon control in a narrow organ duct where insertion of the endoscope is difficult to insert in the processing of FIG. The figure for demonstrating the modification of the balloon control in the wide organ duct which can insert the insertion part of the endoscope in the process of FIG. The figure which shows the proximal balloon provided in the insertion part front-end | tip of the endoscope which concerns on 2nd Embodiment. The figure which shows arrangement | positioning structure of the air supply / intake part which expands / contracts the proximal end balloon of FIG. 13, and the advancing / retreating drive part which moves a moving member.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 ... Image diagnostic system, 10 ... Image diagnostic apparatus, 32 ... Operation control part, 100 ... Endoscope, 114,602 ... Insertion part, 138 ... Forceps insertion part, 156 ... Forceps opening, 200 ... Endoscope processor, 230 DESCRIPTION OF SYMBOLS Image synthesizing unit, 300 Light source device, 400 OCT processor, 500 Monitor device, 600 OCT probe, 651, 652 Tip balloon, 653, 654 Base balloon, 655 Moving member, 656 Bar member 657 ... Restriction member, 661, 662, 663, 664 ... Air supply / intake pipe, 671 ... Advance / retreat drive, 672 ... Air supply / intake part

Claims (18)

Provided on the side of the distal end of the elongated and substantially cylindrical probe insertion portion, and has a light opening that irradiates the measurement light of the luminal organ in the body cavity and enters the reflected light of the measurement light from the measurement light An optical probe;
A gap between the light opening and the tissue surface of the luminal organ is maintained at a position closer to the distal end than the light opening and a position closer to the proximal end than the light opening, and the fold structure on the tissue surface is stretched. Fold extension means,
An optical probe device Ru provided with,
The pleat extension means is
A first tip balloon provided at a tip position on the first side surface of the tip side surface, located on the tip side from the light opening;
A second tip balloon provided at a tip position of the second side surface of the tip side surface facing the tip position of the first side surface and the radial direction of the probe insertion portion;
Tip balloon inflation means for inflating the first tip balloon and the second tip balloon;
A first proximal balloon located on the proximal side of the light opening and on the distal side of the first side surface, provided at the proximal side of the first side surface of the side surface of the probe insertion portion;
A second proximal balloon provided at a second lateral base end position of the side surface of the probe insertion part opposite to the first lateral side base end position in the radial direction of the probe insertion part;
Proximal balloon inflation means for inflating the first proximal balloon and the second proximal balloon;
Balloon moving means for moving the first proximal balloon and the second proximal balloon in the longitudinal direction of the probe insertion portion;
Consists of
An optical probe apparatus comprising movement restriction means for restricting movement of the first proximal balloon and the second proximal balloon by the balloon moving means. A light opening provided on the distal end side surface of the elongated and substantially cylindrical probe insertion portion for irradiating the measurement light of the hollow organ in the body cavity with the reflected light of the measurement light from the measurement light. An optical probe having,
An endoscope that images the inside of a body cavity having a treatment instrument channel through which the optical probe is inserted;
A gap between the optical opening and the tissue surface of the luminal organ is maintained at the distal end of the probe insertion portion and the endoscope insertion portion on the distal side of the optical opening, and a fold structure on the tissue surface is provided. A means to stretch the folds,
An optical probe device comprising: Provided on the side of the distal end of the elongated and substantially cylindrical probe insertion portion, and has a light opening that irradiates the measurement light of the luminal organ in the body cavity and enters the reflected light of the measurement light from the measurement light An optical probe;
A gap between the light opening and the tissue surface of the luminal organ is maintained at a position closer to the distal end than the light opening and a position closer to the proximal end than the light opening, and the fold structure on the tissue surface is stretched. Fold extension means,
An optical probe device comprising:
The pleat extension means is
A first tip balloon provided at a tip position on the first side surface of the tip side surface, located on the tip side from the light opening;
A second tip balloon provided at a tip position of the second side surface of the tip side surface facing the tip position of the first side surface and the radial direction of the probe insertion portion;
Tip balloon inflation means for inflating the first tip balloon and the second tip balloon;
A first proximal balloon located on the proximal side of the light opening and on the distal side of the first side surface, provided at the proximal side of the first side surface of the side surface of the probe insertion portion;
A second proximal balloon provided at a second lateral base end position of the side surface of the probe insertion part opposite to the first lateral side base end position in the radial direction of the probe insertion part;
Proximal balloon inflation means for inflating the first proximal balloon and the second proximal balloon;
Balloon moving means for moving the first proximal balloon and the second proximal balloon in the longitudinal direction of the probe insertion portion;
Tona is,
A distal-side inflation control means for controlling the inflation of the first distal balloon and the second distal balloon by the distal balloon inflation means; and the first proximal balloon and the second proximal balloon by the proximal balloon inflation means. A proximal-side inflation control means for controlling inflation; and a movement control means for controlling movement of the first proximal balloon and the second proximal balloon by the balloon moving means;
The movement control means controls the balloon movement means after inflation control of the first distal balloon and the second distal balloon by the distal side inflation control means so that the first proximal balloon and the second proximal balloon are moved. It moves in the longitudinal axis direction of the probe insertion portion, and after this movement control, the proximal-side inflation control means controls the proximal-balloon inflation means to inflate the first proximal balloon and the second proximal balloon,
The movement control means controls the balloon moving means after inflation control of the first proximal balloon and the second proximal balloon by the proximal inflation control means to control the first proximal balloon and the second proximal end. An optical probe device, wherein a balloon is moved in a proximal direction of a longitudinal axis of the probe insertion portion. The pleat extension means is
A first tip balloon provided at a tip position on the first side surface of the tip side surface, located on the tip side from the light opening;
A second tip balloon provided at a tip position of the second side surface of the tip side surface facing the tip position of the first side surface and the radial direction of the probe insertion portion;
Tip balloon inflation means for inflating the first tip balloon and the second tip balloon;
A first proximal balloon provided on a first side proximal position of the distal side of the endoscope insertion portion on the first lateral distal position side;
A second base end balloon provided at a second side base end position of the side surface of the endoscope insertion part opposite to the first side base end position in the radial direction of the endoscope insertion part;
Proximal balloon inflation means for inflating the first proximal balloon and the second proximal balloon;
Balloon moving means for moving the first proximal balloon and the second proximal balloon in the longitudinal axis direction of the probe insertion portion when inserted into the treatment instrument channel;
The optical probe device according to claim 2, comprising: 5. The optical probe device according to claim 4 , further comprising movement restriction means for restricting movement of the first proximal balloon and the second proximal balloon by the balloon moving means. The balloons of the first distal balloon, the second distal balloon, the first proximal balloon, and the second proximal balloon are made of natural rubber , and any one of claims 3 to 5 The optical probe device according to one. A distal-side inflation control means for controlling the inflation of the first distal balloon and the second distal balloon by the distal balloon inflation means; and the first proximal balloon and the second proximal balloon by the proximal balloon inflation means. The apparatus further comprises: a proximal-side inflation control means for controlling inflation; and a movement control means for controlling movement of the first proximal balloon and the second proximal balloon by the balloon moving means. Item 7. The optical probe device according to any one of Items 1 and 4 to 6.   The distal-side inflation control means and the proximal-side inflation control means control the distal balloon inflation means and the proximal balloon inflation means, and the first distal balloon, the second distal balloon, and the first proximal balloon. The optical probe device according to claim 7, wherein each of the second proximal balloon and the second proximal balloon are inflated and brought into contact with an inner wall of the luminal organ.   The distal side inflation control means controls the distal balloon inflation means, inflates one of the first distal balloon and the second distal balloon larger than the other, abuts against the inner wall of the luminal organ, The proximal-side inflation control means controls the proximal balloon inflation means, and the first distal balloon on the side where the first distal balloon or the second distal balloon on which the distal inflation control means is inflated more greatly is disposed. 9. The optical probe device according to claim 8, wherein one of the proximal balloon and the second proximal balloon is inflated larger than the other and is brought into contact with the inner wall of the luminal organ.   The movement control means controls the balloon movement means after inflation control of the first distal balloon and the second distal balloon by the distal side inflation control means so that the first proximal balloon and the second proximal balloon are moved. It moves in the longitudinal axis direction of the probe insertion portion, and after this movement control, the proximal-side inflation control means controls the proximal-balloon inflation means to inflate the first proximal balloon and the second proximal balloon. The optical probe device according to claim 7, wherein:   The movement control means controls the balloon moving means after inflation control of the first proximal balloon and the second proximal balloon by the proximal inflation control means to control the first proximal balloon and the second proximal end. The optical probe device according to claim 10, wherein the balloon is moved in the proximal direction of the longitudinal axis of the probe insertion portion. An operation method of the optical probe device according to any one of claims 1 and 3 to 6,
The tip balloon inflation means is controlled by the tip side inflation control means, and air supply and suction to the first tip balloon and the second tip balloon are controlled to inflate the first tip balloon and the second tip balloon. A tip side expansion control step to be controlled;
The proximal balloon inflation means is controlled by the proximal inflation control means, and air supply and intake to the first proximal balloon and the second proximal balloon are controlled, and the first proximal balloon and the second balloon are controlled . A proximal inflation control step for controlling the inflation of the proximal balloon;
The movement controlling means controls the balloon moving unit, a movement control step of controlling the movement of the first proximal balloon and the second proximal balloon,
A method of operating an optical probe device, comprising: The movement controlling step after inflation control of the first distal balloon and said second distal balloon by the distal-side expansion control step, by controlling the balloon moving means by said movement control means, the first proximal balloon and the The second proximal balloon is moved in the longitudinal axis direction of the probe insertion portion, and after the movement control , the proximal inflation control step controls the proximal balloon inflation means by the proximal inflation control means , 13. The method of operating an optical probe device according to claim 12, wherein the first proximal balloon and the second proximal balloon are inflated. In the movement control step, after the inflation control of the first proximal balloon and the second proximal balloon by the proximal-side inflation control step , the balloon movement means is controlled by the movement control means , and the first proximal end 14. The method of operating an optical probe device according to claim 13, wherein the balloon and the second proximal balloon are moved in the proximal direction of the longitudinal axis of the probe insertion portion. The distal side inflation control step and the proximal side inflation control step control the distal balloon inflation unit by the distal side inflation control unit and control the proximal balloon inflation unit by the proximal side inflation control unit , 15. The first distal balloon, the second distal balloon, the first proximal balloon, and the second proximal balloon are each inflated and brought into contact with the inner wall of the luminal organ. Method of operating the optical probe apparatus of the present invention. The distal-side expansion control step, the tip balloon inflation means controlled by one larger expansion than the other and one of said second distal balloon and said first distal balloon the luminal organ by the distal-side expansion control means In the proximal end side inflation control step , the proximal end side inflation control means controls the proximal end balloon inflation means by the proximal end side inflation control means so that the first distal balloon or the second distal balloon is further inflated. The one of the first proximal balloon and the second proximal balloon on the side on which is disposed is inflated larger than the other and brought into contact with the inner wall of the luminal organ. A method of operating the optical probe device. The movement controlling step after inflation control of the first distal balloon and said second distal balloon by the distal-side expansion control step, by controlling the balloon moving means by said movement control means, the first proximal balloon and the The second proximal balloon is moved in the longitudinal axis direction of the probe insertion portion, and after this movement control, the proximal inflation control step controls the proximal balloon inflation means by the proximal inflation control means , The method of operating an optical probe device according to any one of claims 12 to 16, wherein the first proximal balloon and the second proximal balloon are inflated. The movement controlling step controls said proximal balloon inflation means Ri by said proximal side expansion control means, after the expansion control of the first proximal balloon and the second proximal balloon, the movement control unit by controlling the balloon moving means, the light according to the first proximal balloon and the second proximal balloon to claim 17, characterized in that moving the proximal direction of the longitudinal axis of the probe insertion portion Method of operating the probe device.

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