JP2011072401A - Optical probe and endoscope apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To advance a probe along a guidewire to a lesion, to observe a distal part and to obtain an image without guidewire artifacts by pulling back the guidewire to a handle portion and pushing out an imaging core to a distal end portion so as to observe a distal part. <P>SOLUTION: A sheath part of an OCT probe 600 includes an imaging core lumen 681 that houses the image core inside along the longitudinal axis of the sheath part of the OCT probe 600, and a guidewire lumen 680 disposed approximately parallel to a distal part of the imaging core lumen 681. Both lumens 680 and 681 are connected in a separated state by a tubular partition wall member 692 composed of an optically transparent and flexible material at the distal end portion. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

    The present invention relates to an optical probe and an endoscope apparatus that acquire an optical coherence tomographic image in a body cavity, and more specifically, an optical probe having a guide wire lumen through which a guide wire that assists insertion into a body cavity can be inserted, and an endoscope The present invention relates to a mirror device.

Conventionally, image diagnosis for rendering a tomographic image of a living body by inserting an optical probe into a body cavity such as a blood vessel, a bile duct, or a pancreatic duct and performing radial scanning has been widely performed. As an example, a probe containing an optical fiber with an optical lens and an optical mirror attached to the distal end is inserted into the body cavity, and light is emitted into the body cavity while radially scanning the optical mirror disposed on the distal end side of the optical fiber. 2. Description of the Related Art An optical coherence tomography (OCT: Optical Coherent Tomography) that draws a cross-sectional image of a body cavity based on the reflected light from the light is used (Patent Document 1).

  When inserting these probes into body cavities, it is common to place a guide wire in front of the probe and place it in the affected area, and insert the probe to the affected area along the guide wire. FIG. 9 shows a schematic sectional view of a probe having a guide wire lumen.

  On the other hand, in an ultrasonic probe having a structure that is relatively similar to the OCT probe, a guide wire lumen and an image core lumen that houses an image core that houses a sensor or the like are combined at the tip to form a single lumen. There has also been proposed a configuration that makes it possible to exclusively use a common lumen in which an image core lumen is shared (Patent Document 2).

  FIGS. 10 and 11 are schematic sectional views of a probe having a common lumen in which a guide wire lumen and an image core lumen are made common. In the case of Patent Document 2, when transmitting the probe to the observation unit, the image core is drawn into the image core lumen, and the common lumen is used as a guide wire lumen, thereby improving the probe insertability. By drawing the guide wire to the guide wire lumen and sending the image core to the common lumen at the tip, it is possible to provide a cross-sectional image at the probe tip.

Patent No. 4021975 Japanese Patent No. 3367666

  However, Patent Document 1 discloses disposing a guide wire lumen at the front portion of the image core lumen. However, since there is a guide wire lumen in front of the image core lumen, it is possible to observe a cross section of the tip portion. Can not. In addition, since the image core and the guide wire are parallel when observing, artifacts of the guide wire appear on the screen.

  That is, when the guide wire lumen is provided in front of the image core lumen as shown in FIG. 9, the optical member cannot be disposed at the tip of the probe, and the image of the tip cannot be observed. On the other hand, at the time of diagnosis, there is a desire to depict as far as possible the tip of the observed lumen. Further, when this configuration is used, there is a problem that artifacts of the guide wire are drawn in the image at the time of observation, and further, the tissue behind the guide wire cannot be observed.

  Further, Patent Document 2 discloses an ultrasonic probe (ultrasonic catheter) having a guide wire lumen and an image core lumen and having both lumens coupled at the tip, but this technique is applied to an optical probe. When applied, since the tip of the image core lumen is open, a normal image cannot be obtained due to the infiltration of blood, body fluid, etc. into the image core lumen.

  That is, when the technique of combining the guide wire lumen and the image core lumen at the tip portion as in the ultrasonic probe disclosed in Patent Document 2 is applied to the optical probe, as shown in FIGS. This is impossible because the distal end of the body is opened, blood and body fluid enter the image core, and images cannot be drawn normally.

  The present invention has been made in view of such circumstances, and allows the probe to be advanced to the affected part along the guide wire, pulls the guide wire back to the proximal part, and pushes the image core to the distal end part. Thus, an object of the present invention is to provide an optical probe and an endoscopic device that can observe the distal portion and can obtain an image free from artifacts of the guide wire.

  In order to achieve the object, the optical probe according to claim 1 includes an optical fiber and an optical component attached to a distal end portion of the optical fiber in a sheath inserted into a body cavity. An optical probe for emitting light transmitted through the optical component toward a living tissue in the body cavity from the optical component, wherein the sheath accommodates the optical fiber so as to be movable forward and backward along a longitudinal axis. A guide wire lumen disposed substantially parallel to a distal portion of the image core lumen, a flexible and light transmissive partition wall that separates the image core lumen and the guide wire lumen, and the image core And a pressure increasing / decreasing port at the proximal portion of the lumen for increasing / decreasing the pressure inside the image core lumen.

  The optical probe according to claim 1, wherein the flexible and light transmissive partition wall separates the image core lumen and the guide wire lumen, and the pressure increasing / decreasing port is in a proximal portion of the image core lumen. By applying pressure to the inside of the image core lumen, the probe can be advanced along the guide wire to the affected area, the guide wire is pulled back to the hand, and the image core is pushed out to the distal end. It is possible to obtain an image free from artifacts of the guide wire while allowing observation of the portion.

  The optical probe according to claim 1, wherein the image core lumen and the guide wire lumen are arranged along the longitudinal axis at the most distal portion, as in the optical probe according to claim 2. The image core lumen is hermetically sealed except at the pressure-increasing / decreasing port portion. When the image core lumen is depressurized from at least the pressure-increasing / decreasing port, the partition wall closes the image core lumen, and the distal-most portion is in the image. It is preferable to function as a core lumen.

  The optical probe according to claim 1, wherein the image core lumen and the guide wire lumen are arranged along the longitudinal axis at the most distal portion, as in the optical probe according to claim 3. The image core lumen is hermetically sealed except for the pressure / reduction port portion, and when the image core lumen is pressurized at least from the pressure / reduction port, the partition wall closes the guide wire lumen, and the most distal portion is It is preferable to function as an image core lumen.

  The optical probe according to claim 1, wherein the image core lumen and the guide wire lumen are arranged along the longitudinal axis at the most distal portion. The image core lumen is hermetically sealed except at the pressure-increasing / decreasing port portion, and when the image core lumen is depressurized from the pressure-increasing / decreasing port, the partition wall closes the image core lumen, and the most distal portion is guided in the guide When functioning as a wire lumen and pressurizing the image core lumen from the pressure increasing / decreasing port, it is preferable that the partition wall closes the guide wire lumen and causes the most distal portion to function as the image core lumen.

  The optical probe according to any one of claims 1 to 4, wherein the optical fiber is disposed in a drive shaft that rotates and rotates the optical component. It is preferable to perform radial scanning in the body cavity by driving.

  The optical probe according to claim 5, wherein the drive shaft is movable along the longitudinal axis, and the optical component is rotationally driven and axially driven. Thus, it is preferable to perform spiral scanning in the body cavity.

  The optical probe according to any one of claims 1 to 6, as in the optical probe according to claim 7, wherein the optical component substantially represents a traveling direction of light transmitted through the optical fiber. It is preferable to provide a ball lens having a reflecting surface that bends at a right angle.

  The optical probe according to any one of claims 1 to 7, as in the optical probe according to claim 8, wherein the optical fiber transmits a wavelength-swept laser beam.

  An endoscope apparatus according to claim 9 is characterized in that the optical probe according to any one of claims 1 to 8 and the sheath of the optical probe are inserted into a treatment instrument channel of the endoscope. To do.

  As described above, according to the present invention, the probe can be advanced to the affected part along the guide wire, the guide wire is pulled back to the hand part, and the image core is pushed out to the distal end part. There is an effect that it is possible to obtain an image in which the position portion can be observed and the guide wire is free from artifacts.

The block diagram which shows the internal structure of the OCT probe and OCT processor which concern on embodiment of this invention Sectional drawing which shows the structure of the optical rotary joint which connects the rotation side optical fiber FB1 of FIG. 1 is a cross-sectional view of the sheath portion of the OCT probe of FIG. 1 when the flexible partition member is contracted The figure which shows the AA line cross section of FIG. The figure which shows the BB line cross section of FIG. 1 is a cross-sectional view of the sheath portion of the OCT probe of FIG. 1 when the flexible partition member is expanded. The figure which shows the CC line cross section of FIG. The figure which shows the diagnostic imaging apparatus used together with the endoscope apparatus which can apply the OCT probe of FIG. Cross-sectional schematic diagram of a probe having a conventional guidewire lumen First cross-sectional schematic diagram of a probe having a common lumen in which a conventional guide wire lumen and an image core lumen are made common Second cross-sectional schematic diagram of a probe having a common lumen in which a conventional guide wire lumen and an image core lumen are made common

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings.

As shown in FIG. 1, the OCT probe 600 and the OCT processor 400 of the present embodiment are for acquiring an optical tomographic image of a measurement object by an optical coherence tomography (OCT) measurement method.

[OCT processor]
The OCT processor 400 includes a first light source (first light source unit) 12 that emits light La for measurement, and a light La emitted from the first light source 12 as measurement light (first light flux) L1. An optical fiber coupler (branching / combining unit) 14 that branches to the reference light L2 and combines the return light L3 from the measurement target S that is the subject and the reference light L2 to generate the interference light L4, and an optical fiber coupler The OCT probe 600 including the rotation-side optical fiber FB1 that guides the measurement light L1 branched at 14 to the measurement target and guides the return light L3 from the measurement target, and the measurement light L1 to the rotation-side optical fiber FB1. The fixed-side optical fiber FB2 that waves and guides the return light L3 guided by the rotation-side optical fiber FB1, and the rotation-side optical fiber FB1 can be rotated with respect to the fixed-side optical fiber FB2. An optical connector 18 that connects and transmits the measurement light L1 and the return light L3, an interference light detection unit 20 that detects the interference light L4 generated by the optical fiber coupler 14 as an interference signal, and is detected by the interference light detection unit 20 The processing unit 22 acquires the optical structure information by processing the received interference signal. In addition, an image is displayed on the monitor device 500 based on the optical structure information acquired by the processing unit 22.

  The OCT processor 400 also includes a second light source (second light source unit) 13 that emits aiming light (second light flux) Le for indicating a mark of measurement, and an optical path that adjusts the optical path length of the reference light L2. A length adjusting unit 26, an optical fiber coupler 28 that splits the light La emitted from the first light source 12, and detection units 30a and 30b that detect return lights L4 and L5 combined by the optical fiber coupler 14, And an operation control unit 32 for inputting various conditions to the processing unit 22 and changing settings.

  In the OCT processor 400 shown in FIG. 1, various lights including the above-described emission light La, aiming light Le, measurement light L1, reference light L2, return light L3, and the like are guided between components such as optical devices. Various optical fibers FB (FB3, FB4, FB5, FB6, FB7, FB8, etc.) including the rotation side optical fiber FB1 and the fixed side optical fiber FB2 are used as light paths for wave transmission.

  The first light source 12 emits laser light or low-coherence light for OCT measurement. The first light source 12 emits laser light La having a wavelength of 1.3 μm at a constant period, for example. This is a light source that emits light while sweeping. The first light source 12 includes a light source 12a that emits laser light or low-coherence light La, and a lens 12b that condenses the light La emitted from the light source 12a. As will be described in detail later, the light La emitted from the first light source 12 is divided into the measurement light L1 and the reference light L2 by the optical fiber coupler 14 through the optical fibers FB4 and FB3, and the measurement light L1 is the light. Input to the connector 18.

  Further, the second light source 13 emits visible light so as to make it easy to confirm the measurement site as the aiming light Le. For example, red semiconductor laser light with a wavelength of 0.66 μm, He—Ne laser light with a wavelength of 0.63 μm, blue semiconductor laser light with a wavelength of 0.405 μm, or the like can be used. Therefore, the second light source 13 includes, for example, a semiconductor laser 13a that emits red, blue, or green laser light and a lens 13b that collects the aiming light Le emitted from the semiconductor laser 13a. The aiming light Le emitted from the second light source 13 is input to the optical connector 18 through the optical fiber FB8.

  In the optical connector 18, the measurement light L 1 and the aiming light Le are combined and guided to the rotation side optical fiber FB 1 in the OCT probe 600.

  The optical fiber coupler (branching / combining unit) 14 is composed of, for example, a 2 × 2 optical fiber coupler, and is optically connected to the fixed-side optical fiber FB2, the optical fiber FB3, the optical fiber FB5, and the optical fiber FB7, respectively. ing.

  The optical fiber coupler 14 splits the light La incident from the first light source 12 through the optical fibers FB4 and FB3 into measurement light (first light flux) L1 and reference light L2, and the measurement light L1 is fixed side light. The light is incident on the fiber FB2, and the reference light L2 is incident on the optical fiber FB5.

  Furthermore, the optical fiber coupler 14 is incident on the optical fiber FB5, is subjected to frequency shift and optical path length change by the optical path length adjusting unit 26 described later, and is returned by the optical fiber FB5 and acquired by the OCT probe 600 described later. Then, the light L3 guided from the fixed side optical fiber FB2 is multiplexed and emitted to the optical fiber FB3 (FB6) and the optical fiber FB7.

  The OCT probe 600 is connected to the fixed optical fiber FB2 via the optical connector 18, and the measurement light L1 combined with the aiming light Le is rotated from the fixed optical fiber FB2 via the optical connector 18. The light enters the side optical fiber FB1. The measurement light L1 combined with the incident aiming light Le is transmitted by the rotation side optical fiber FB1, and is irradiated to the measurement object S. Then, the return light L3 from the measuring object S is acquired, the acquired return light L3 is transmitted by the rotation side optical fiber FB1, and is emitted to the fixed side optical fiber FB2 via the optical connector 18.

  The optical connector 18 combines the measurement light (first light beam) L1 and the aiming light (second light beam) Le.

  The interference light detection unit 20 is connected to the optical fibers FB6 and FB7, and uses the interference lights L4 and L5 generated by combining the reference light L2 and the return light L3 by the optical fiber coupler 14 as interference signals. It is to detect.

  Here, the OCT processor 400 is provided on the optical fiber FB6 branched from the optical fiber coupler 28. The detector 30a detects the light intensity of the interference light L4, and the light of the interference light L5 on the optical path of the optical fiber FB7. And a detector 30b for detecting the intensity.

  The interference light detection unit 20 performs Fourier transform on the interference light L4 detected from the optical fiber FB6 and the interference light L5 detected from the optical fiber FB7 based on the detection results of the detectors 30a and 30b, thereby measuring the measurement target S. The intensity of the reflected light (or backscattered light) at each depth position is detected.

  From the interference signal extracted by the interference light detection unit 20, the processing unit 22 is a region where the OCT probe 600 and the measurement target S are in contact at the measurement position, more precisely, a probe outer cylinder (described later) of the OCT probe 600. A region where the surface and the surface of the measuring object S can be considered to be in contact with each other is detected, optical structure information is acquired from the interference signal detected by the interference light detection unit 20, and optical solids are obtained based on the acquired optical structure information. A structure image is generated, and an image obtained by performing various processes on the optical three-dimensional structure image is output to the monitor device 500. The detailed configuration of the processing unit 22 will be described later.

  The optical path length adjustment unit 26 is disposed on the emission side of the reference light L2 of the optical fiber FB5 (that is, the end of the optical fiber FB5 opposite to the optical fiber coupler 14).

  The optical path length adjustment unit 26 includes a first optical lens 80 that converts the light emitted from the optical fiber FB5 into parallel light, a second optical lens 82 that condenses the light converted into parallel light by the first optical lens 80, and The reflection mirror 84 that reflects the light collected by the second optical lens 82, the base 86 that supports the second optical lens 82 and the reflection mirror 84, and the base 86 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 80 and the second optical lens 82.

  The first optical lens 80 converts the reference light L2 emitted from the core of the optical fiber FB5 into parallel light, and condenses the reference light L2 reflected by the reflection mirror 84 on the core of the optical fiber FB5.

  The second optical lens 82 condenses the reference light L2 converted into parallel light by the first optical lens 80 on the reflection mirror 84 and makes the reference light L2 reflected by the reflection mirror 84 parallel light. Thus, the first optical lens 80 and the second optical lens 82 form a confocal optical system.

  Further, the reflection mirror 84 is disposed at the focal point of the light collected by the second optical lens 82 and reflects the reference light L2 collected by the second optical lens 82.

  As a result, the reference light L2 emitted from the optical fiber FB5 becomes parallel light by the first optical lens 80 and is condensed on the reflection mirror 84 by the second optical lens 82. Thereafter, the reference light L2 reflected by the reflection mirror 84 becomes parallel light by the second optical lens 82 and is condensed by the first optical lens 80 on the core of the optical fiber FB5.

  The base 86 fixes the second optical lens 82 and the reflecting mirror 84, and the mirror moving mechanism 88 moves the base 86 in the optical axis direction of the first optical lens 80 (the direction of arrow A in FIG. 2). .

  By moving the base 86 in the direction of arrow A with the mirror moving mechanism 88, the distance between the first optical lens 80 and the second optical lens 82 can be changed, and the optical path length of the reference light L2 can be adjusted. Can do.

  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 and the like in the processing unit 22 based on an operator instruction input from the input unit.

  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. In addition, the operation control unit 32 controls the operation of the first light source 12, the second light source 13, the optical connector 18, the interference light detection unit 20, the optical path length, the detection units 30a and 30b, and sets various conditions. May be. As shown in FIG. 2, the rotation side optical fiber FB1 and the fixed side optical fiber FB2 are connected by an optical connector 18, and the rotation of the rotation side optical fiber FB1 is not transmitted to the fixed side optical fiber FB2. Connected. The rotation-side optical fiber FB1 is arranged so as to be rotatable with respect to the image core lumen 681 and movable in the axial direction of the image core lumen 681.

  The torque transmission coil 624 is fixed to the outer periphery of the rotation side optical fiber FB1. The rotation side optical fiber FB1 and the torque transmission coil 624 are connected to the optical rotary joint of the optical connector 18.

  Further, the rotation-side optical fiber FB1, the torque transmission coil 624, and the ball lens (optical lens) 690 (see FIG. 3) are moved inside the image core lumen 681 by an arrow S1 by an advancing / retreating drive unit provided later on the optical connector 18. It is configured to be movable in the direction (forceps opening direction) and the S2 direction (tip direction of the image core lumen 681).

  The image core lumen 681 is fixed to the fixing member 670. On the other hand, the rotation side optical fiber FB1 and the torque transmission coil 624 are connected to a rotation cylinder 656, and the rotation cylinder 656 is configured to rotate via a gear 654 in accordance with the rotation of the motor 652. . The rotary cylinder 656 is connected to the optical rotary joint of the optical connector 18, and the measurement light L1 and the return light L3 are transmitted between the rotary optical fiber FB1 and the fixed optical fiber FB2 via the optical connector 18.

  Further, the frame 650 containing these includes a support member 662, and the support member 662 has a screw hole (not shown). The frame 650 is engaged with a forward / backward moving ball screw 664 in a screw hole (not shown) of the support member 662, and a motor 660 is connected to the forward / backward moving ball screw 664 so that the screw hole and the forward / backward moving ball screw 664 are connected. The motor 660 or the like constitutes an advance / retreat drive unit as an advance / retreat moving means. Accordingly, the advancing / retreating drive unit of the optical rotary joint of the optical connector 18 moves the frame 650 forward and backward by rotationally driving the motor 660, thereby rotating the rotation side optical fiber FB1, the torque transmission coil 624, the fixing member 626, and the ball lens. It is possible to move 628 in the S1 and S2 directions in FIG.

  The motor 660 is driven back and forth at a predetermined pitch, for example, at an interval of 1 mm, and the motor 652 rotates the rotation side optical fiber FB1, the torque transmission coil 624, and the ball lens 628 once for each predetermined pitch. The measuring object S is irradiated with the measuring light L1 by radial scanning.

  In the OCT probe 600, the rotation side optical fiber FB1 and the torque transmission coil 624 are rotated by the optical rotary joint of the optical connector 18 in the direction of arrow R in FIG. The measurement light L1 emitted is irradiated to the measurement object S while performing radial scanning in the direction of arrow R (circumferential direction of the image core lumen 681), and the return light L3 is acquired.

  Thereby, the desired site | part of the measuring object S can be caught correctly in the perimeter of the circumferential direction of the image core lumen 681, and the return light L3 which reflected the measuring object S can be acquired.

  Furthermore, when acquiring a plurality of optical structure information for generating an optical three-dimensional structure image, the ball lens 628 is moved within the movable range in the direction of arrow S1 in FIG. Move to the end and move in the S2 direction by a predetermined amount while acquiring optical structure information consisting of tomograms, or move by alternately repeating the acquisition of optical structure information and the predetermined amount movement in the S2 direction in FIG. Move to the end of the range.

  In this manner, a plurality of pieces of optical structure information in a desired range can be obtained for the measurement object S, and an optical three-dimensional structure image can be obtained based on the obtained pieces of light structure information.

  That is, the optical structure information in the depth direction (first direction) of the measurement target S is acquired from the interference signal, and the measurement target S is radially scanned in the direction of the arrow R in FIG. Thus, it is possible to obtain optical structure information on the scan plane composed of the depth direction (first direction) of the measuring object S and the direction (second direction) substantially orthogonal to the depth direction, Furthermore, by moving the scan plane along a direction (third direction) substantially orthogonal to the scan plane, a plurality of pieces of optical structure information for generating an optical three-dimensional structure image can be acquired.

  As shown in FIG. 3, the image core of the present OCT probe 600 is composed of a drive shaft 682, an optical fiber FB1 and a torque transmission coil 624 in the drive shaft 682, and a ball lens 690 provided at the tip of the optical fiber FB1. Has the same configuration as that of the conventional optical probe, but in the image core of the present embodiment, in the drive shaft 682, the optical fiber FB1 having the ball lens 690 disposed at the tip thereof is provided with the torque disposed outside thereof. The transmission coil 624 is rotated to rotate and perform radial scanning. Further, the drive shaft 682 simultaneously performs axial scanning by a linear motion mechanism disposed at the hand portion, and performs spiral scanning (see FIG. 2).

  The sheath part of the OCT probe 600 is a main component according to the present embodiment. The sheath portion of the OCT probe 600 is a blade tube with a metal mesh 698 on the inner side on the hand side, and the lumen of the sheath portion can be secured even when the forceps channel raising mechanism of the endoscope is operated. It has become.

  In addition, the sheath portion of the OCT probe 600 includes an image core lumen 681 that houses (extends) the image core along the longitudinal axis of the sheath portion of the OCT probe 600 and a distal portion of the image core lumen 681. The guide wire lumen 680 is arranged substantially in parallel (see FIG. 4 which is a cross section taken along the line AA in FIG. 3). Both lumens 680 and 681 are connected in a separated state by a cylindrical partition wall member 692 made of a light-transmitting and flexible material such as silicone rubber at the tip. Here, silicone rubber is used, but the material is not limited to this material, and other materials such as latex rubber, nylon, and PET may be used.

  The image core lumen 681 is linearly fixed to the partition wall member 692 at the lower side, and the distal side is sealed, as shown in FIG. Further, a pressure / decompression port 694 is provided in the hand portion, and although not shown, it is possible to reduce the pressure in the image core lumen 681 by connecting a syringe with a lock or an indeflator. It has become.

  Hereinafter, an operation when the OCT probe 600 is inserted into an affected part will be described. The image core lumen 681 is decompressed by connecting a syringe (not shown) with a lock to the pressure increasing / decreasing port 694 and sucking with the syringe. At that time, the flexible partition member 692 contracts so that the volume of the image core lumen 681 is minimized, and the guide wire lumen 680 is opened to the tip. Therefore, by passing the end portion of the guide wire 700 inserted in advance to the affected part through the guide wire lumen 680 and pushing it along the guide wire 700, the OCT probe 600 can be easily advanced to the affected part.

  Next, the operation during observation will be described with reference to FIG. When the OCT probe 600 is placed in the affected area, the guide wire 700 is pulled to the proximal portion of the guide wire lumen 680. At this time, the guide wire 700 is not pulled out from the guide wire lumen 680 while confirming the contrast marker 699 on fluoroscopy.

  Next, by pressurizing the image core lumen 681 using a syringe, the space of the image core lumen 681 is formed up to the tip as shown in FIG. In this state, the drive shaft 682 is advanced to the forefront so that observation is possible. Next, by rotating the drive shaft 682, radial scanning is performed, and at the same time, scanning is performed at a constant speed in the axial direction, thereby enabling a spiral operation and acquiring three-dimensional tomographic image data of the body cavity. .

  Note that the OCT probe 600 of the present embodiment can be used not only as a blood vessel catheter but also in an image diagnostic apparatus used in combination with an endoscope apparatus.

  More specifically, as shown in FIG. 8, the diagnostic imaging apparatus 10 used in combination with the OCT probe 600 and the endoscope apparatus of the present embodiment mainly includes an endoscope 100, an endoscope processor 200, a light source device 300, a living body. It comprises an OCT processor 400 as a tomographic image generation device and a monitor device 500 as a display means. 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.

  The hand operation unit 112 is provided with a forceps insertion portion 138, and this forceps insertion portion 138 communicates with a forceps port 156 of the distal end portion 144 via a forceps channel (not shown) provided in the insertion portion 114. Has been. In the diagnostic imaging apparatus 10, the OCT probe 600 as a probe is inserted from the forceps insertion portion 138, and the OCT probe 600 is led out from the forceps opening 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.

  At the distal end portion 144 of the endoscope 100, an observation optical system 150, an illumination optical system 152, and a CCD (not shown) are disposed.

  The observation optical system 150 forms an image of a subject on a light receiving surface (not shown) of the CCD, and the CCD converts the subject image formed on the light receiving surface into an electric signal by each light receiving element. The CCD 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.

  The light source device 300 causes visible light to enter a light guide (not shown). One end of the light guide is connected to the light source device 300 via the LG connector 120, and the other end of the light guide faces the illumination optical system 152. The light emitted from the light source device 300 is emitted from the illumination optical system 152 via the light guide, and illuminates the visual field range of the observation optical system 150.

  An image signal output from the CCD is input to the endoscope processor 200 via the electrical connector 110. The analog image signal is converted into a digital image signal in the endoscope processor 200, and necessary processing for displaying on the screen of the monitor device 500 is performed.

  In this manner, 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.

  As described above, in the OCT probe 600 of the present embodiment, the image core can be advanced to the distal end portion, the cross section of the distal end portion can be observed, and the guide wire is pulled back to the front of the observation surface during observation. So no artifacts occur. In addition, since the tip of the image core lumen is sealed, blood or the like does not enter the image core lumen, and an accurate image can be obtained. Therefore, according to the present embodiment, the probe can be advanced to the affected part along the guide wire, the guide wire is pulled back to the hand part, and the image core is pushed out to the tip part, so that the distal part An image that can be observed and that is free of guide wire artifacts can be obtained.

  Although the optical probe and the endoscope apparatus of the present invention have been described in detail above, 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 it is also good.

400 ... OCT processor, 600 ... OCT probe, 680 ... guide wire lumen, 681 ... image core lumen, 692 ... partition member, 694 ... pressure / decompression port, 700 ... guide wire

Claims (9)

An optical fiber and an optical component attached to the distal end of the optical fiber are provided in a sheath inserted into the body cavity, and the light transmitted through the optical fiber is transmitted from the optical component to the living tissue in the body cavity. An optical probe that emits toward
The sheath is
An image core lumen for accommodating the optical fiber so as to advance and retract along the longitudinal axis;
A guide wire lumen disposed substantially parallel to the distal portion of the image core lumen;
A flexible and light-transmitting partition wall that separates the image core lumen and the guidewire lumen;
A pressure increasing / decreasing port at the proximal portion of the image core lumen for increasing / decreasing the pressure inside the image core lumen;
An optical probe characterized by comprising:   The image core lumen and the guide wire lumen are disposed along the longitudinal axis at the most distal portion, and the image core lumen is hermetically sealed except at the pressurization / decompression port portion, and at least from the pressurization / decompression port 2. The optical probe according to claim 1, wherein when the image core lumen is decompressed, the partition wall closes the image core lumen and causes the most distal portion to function as the image core lumen.   The image core lumen and the guide wire lumen are disposed along the longitudinal axis at the most distal portion, and the image core lumen is hermetically sealed except at the pressurization / decompression port portion, and at least from the pressurization / decompression port 2. The optical probe according to claim 1, wherein when the image core lumen is pressurized, the partition wall closes the guide wire lumen and causes the most distal portion to function as the image core lumen.   The image core lumen and the guide wire lumen are disposed along the longitudinal axis at the most distal portion, and the image core lumen is sealed except at the pressure-increasing / decreasing port portion, and When the image core lumen is depressurized, the septum closes the image core lumen, and the most distal portion functions as the guide wire lumen. When the image core lumen is pressurized from the pressure-inducing and depressurizing port, the septum The optical probe according to claim 1, wherein a guide wire lumen is closed, and the most distal portion functions as the image core lumen.   5. The light according to claim 1, wherein the optical fiber is disposed in a drive shaft that is rotationally driven, and the optical cavity is rotationally driven to perform radial scanning in the body cavity. probe.   6. The optical probe according to claim 5, wherein the drive shaft is movable along the longitudinal axis, and spiral scanning is performed in the body cavity by rotationally driving and axially driving the optical component. .   The optical probe according to any one of claims 1 to 6, wherein the optical component includes a ball lens having a reflecting surface that bends the traveling direction of the light transmitted through the optical fiber at a substantially right angle.   The optical probe according to claim 1, wherein the optical fiber transmits wavelength-swept laser light.   An endoscope apparatus, wherein the optical probe according to any one of claims 1 to 8 and the sheath of the optical probe are inserted into a treatment instrument channel of an endoscope.

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