JP2012029912A - Optical probe and optical tomographic imaging device - Google Patents

Abstract

In a tomographic image, it is possible to clearly identify a region (non-signal region) where light does not reach and no deep information is obtained.
A sheath 620 of an OCT probe 600 is provided with a first lumen 630 in which a distal end is closed and an optical lens 628 is accommodated, and an opening 632a is formed at the distal end to perform biopsy or treatment. And a second lumen 632 in which the treatment tool is accommodated. The first and second lumens 630 and 632 are arranged side by side so that the axial directions thereof are parallel to each other, and the first lumen 630 is formed so as to protrude toward the distal end side in the axial direction from the second lumen 632. . An optical lens 628 is disposed on a protrusion 630a that protrudes beyond the second lumen 632 of the first lumen 630, and the partition wall of the protrusion 630a is made of a light-transmitting member and has a uniform thickness. It is comprised in the cylindrical shape which has.
[Selection] Figure 4

Description

  The present invention relates to an optical probe and an optical tomographic imaging apparatus, and more particularly to an optical probe and an optical tomographic imaging apparatus capable of performing biopsy and treatment while observing an optical tomographic image.

  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. In addition, many endoscope apparatuses include a forceps port, and a biopsy or treatment of tissue in the body cavity can be performed by a probe introduced into the body cavity via the forceps port.

  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 living tissue has been advanced. For example, optical coherence tomography (OCT) using interference by low-coherence light has been developed. An optical tomographic imaging apparatus using an optical coherence tomography measurement method 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-coherent light emitted from the light source is divided into measurement light and reference light, the measurement light is irradiated onto the measurement object, and 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.

  Since the OCT probe (optical probe) is inserted into the treatment instrument channel of the endoscope apparatus, the OCT probe (optical probe) is configured to have a smaller diameter than the insertion portion of the endoscope. For this reason, even in regions where the diameter of the lumen such as the bile duct, pancreatic duct, blood vessels, and bronchial ends is small and the insertion part of the endoscope cannot be inserted, optical tomographic images can be observed with the OCT probe. It is possible.

  Therefore, using an OCT probe, even a lesion site in a narrow region in a body cavity that cannot be observed with an endoscope is used for biopsy or treatment while confirming the location of the lesion site from an optical tomographic image. It is desired to be able to do so.

  For example, Patent Document 1 proposes an endoscopic treatment instrument that includes a multi-lumen sheath, an OCT probe is inserted into one lumen, and a biopsy brush (cytodiagnosis brush) is inserted into the other lumen. Has been.

JP 2008-200098 A

  However, in the endoscope treatment tool disclosed in Patent Document 1, an OCT probe is inserted into a multi-lumen sheath, and an optical fiber or an optical lens is further formed in the sheath (probe outer cylinder) of the OCT probe. There is a multiple structure in which the probe body is inserted, and there is a limit to reducing the diameter.

  Therefore, in order to further reduce the diameter, for example, as shown in FIG. 7, it is conceivable to make the sheath 1620 of the OCT probe 1600 multi-lumen. In the configuration shown in the figure, the first and second lumens 1630 and 1632 are juxtaposed in parallel with each other, and the first lumen 1630 protrudes more in the axial direction than the second lumen 1632. Formed. A probe main body including an optical lens 1628 and a rotation-side optical fiber 1650 is inserted into the first lumen 1630, and the tip thereof is blocked to prevent intrusion of body fluid, cleaning fluid, and the like. A biopsy brush 1634 is inserted through the second lumen 1632 as a treatment tool, and an opening 1638a for leading out the biopsy brush 1638 is formed at the tip thereof.

  The optical lens 1628 and the rotation-side optical fiber 1650 are configured to be rotatable in the arrow R2 direction around the axial direction of the rotation-side optical fiber 1650, and in the direction of the arrow S1 (forceps opening direction) parallel to the axis direction, and It is configured to be movable in the S2 direction (the tip direction of the first lumen 630).

  However, in the configuration shown in FIG. 7, a flat surface is formed on a part of the outer wall surface of the projecting portion of the first lumen 1630 (the portion projecting toward the distal end side in the axial direction from the second lumen 1632) 1630a. The thickness of the outer peripheral wall of the first lumen 1630 is configured to be uneven along the circumferential direction. For this reason, when acquiring the return light from the measurement target while scanning the measurement light irradiated to the measurement target from the optical lens 1628, the influence of refraction of the light passing through the sheath 1620 differs depending on the scanning direction of the measurement light. There is a problem that the image quality of the tomographic image is degraded.

  The present invention has been made in view of such circumstances, and it is possible to obtain a good optical tomographic image without the influence of refraction of light passing through the sheath being different depending on the scanning direction of the measurement light. An object of the present invention is to provide an optical probe and an optical tomographic imaging apparatus capable of performing biopsy and treatment while observing an image.

  In order to achieve the object, the optical probe according to claim 1 is in a sheath inserted into the subject, and rotationally scans the measurement light propagating from the light source through the optical fiber around the axis of the optical fiber. In the optical probe provided with an optical system that irradiates the measurement object while receiving the return light from the measurement object and introduces it into the optical fiber, the first end is closed and the optical system is accommodated. A sheath having a lumen and a second lumen in which an opening is formed at a distal end and a treatment tool for performing a biopsy or treatment is formed, and the first and second lumens each other The first lumen is formed in parallel with the axial direction so as to be parallel to each other, and protrudes toward the distal end side in the axial direction from the second lumen. The first lumen is more than the second lumen of the first lumen. Protruding Is the optical system is disposed on the outlet portion, the outer wall of the projecting portion is made of a member having optical transparency, and is characterized by being configured in a cylindrical shape having a uniform wall thickness.

  According to the present invention, the influence of refraction of light passing through the sheath does not differ depending on the scanning direction of the measurement light, the detection accuracy of interference light is improved, and a good optical tomographic image can be obtained. This makes it possible to perform biopsy or treatment while confirming the position of the lesion site from the optical tomographic image even in a lesion site in a narrow region in the body cavity that cannot be observed by the endoscope.

  The optical probe according to claim 1, wherein the focal length of the optical system is determined according to the diameter of the second lumen, and the optical probe is Of the first and second lumens, it is preferable that the second lumen side is pushed so as to be the measurement target side.

  The optical probe according to claim 1 or 2, wherein an amount of protrusion of the treatment instrument that is led out from the opening is restricted to the second lumen. It is preferable that a stopper member is provided, and a protrusion amount of the treatment instrument is regulated by bringing a stopper receiving portion provided in the treatment instrument into contact with the stopper member.

  The optical probe according to any one of claims 1 to 3, as in the optical probe according to claim 4, wherein the sheath is configured to identify a direction of the first or second lumen. Preferably marker means are provided.

  As in the optical probe according to claim 5, in the optical probe according to claim 4, the marker means is provided on the outer wall of the first lumen opposite to the second lumen. It is preferable.

  The optical probe according to any one of claims 1 to 5, wherein the sheath includes at least one fixing balloon, and the optical probe is an object to be measured. It is preferable to fix the optical probe by bringing the fixing balloon into contact with the body cavity wall in the subject when pressed against the body.

  The optical probe according to any one of claims 1 to 6, wherein the treatment instrument is a biopsy brush.

  The optical probe according to any one of claims 1 to 6, wherein the treatment instrument is a radiation marker or a high-frequency marker.

  The optical probe according to any one of claims 1 to 8, wherein the optical system rotates around an axis of the optical fiber as in the optical probe according to claim 9. It is preferable that the measurement light irradiated on the measurement object is scanned while moving in the axial direction, and the movable range in the axial direction of the optical system is included in the protruding portion.

  The optical probe according to any one of claims 1 to 9, as in the optical probe according to claim 10, wherein the sheath is parallel by shifting the tips of two tubular members in the axial direction. It is preferable to have a bonded structure.

  In order to achieve the object, an optical tomographic imaging apparatus according to claim 11, a light splitting unit that splits light emitted from a light source into measurement light and reference light, and the measurement light to be measured Irradiating optical means for irradiating, combining means for combining reflected light from the measurement object by the measuring light irradiated by the irradiating optical means and the reference light, and combining by the combining means Interference light detection means for detecting interference light between the reflected light and the reference light; and image acquisition means for acquiring a tomographic image of the measurement object based on the interference light detected by the interference light detection means. And the irradiation optical means includes the optical probe according to any one of claims 1 to 10.

  According to the present invention, the influence of refraction of light passing through the sheath does not differ depending on the scanning direction of the measurement light, the detection accuracy of interference light is improved, and a good optical tomographic image can be obtained. This makes it possible to perform biopsy or treatment while confirming the position of the lesion site from the optical tomographic image even in a lesion site in a narrow region in the body cavity that cannot be observed by the endoscope.

External view showing an image diagnostic apparatus using the optical tomographic imaging apparatus according to the present embodiment The block diagram which shows the internal structure of the OCT processor of FIG. The perspective view which showed the outline of the front-end | tip part of the OCT probe of FIG. Side sectional view of the OCT probe of FIG. 3 viewed from a direction parallel to the axial direction FIG. 3 is a front sectional view of the OCT probe of FIG. 3 viewed from a direction perpendicular to the axial direction. It is front sectional drawing which showed the other structural example of the front-end | tip part of an OCT probe. The perspective view which showed the outline of the front-end | tip part of the OCT probe which has the sheath made into the multilumen.

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

  FIG. 1 is an external view showing an image diagnostic apparatus using the optical tomographic imaging apparatus according to the present embodiment.

  As shown in FIG. 1, the diagnostic imaging apparatus 10 mainly includes an endoscope 100, an endoscope processor 200, a light source apparatus 300, an OCT processor 400 as an optical tomographic imaging apparatus, and a monitor apparatus 500. Yes. Note that 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.

  The hand operation part 112 is provided with a forceps insertion part 138, and the forceps insertion part 138 communicates with the forceps port 156 of the distal end part 144. In 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 into the OCT processor 400 via the insertion portion 602 inserted from the forceps insertion portion 138 and led out from the forceps opening 156, the operation portion 604 for the operator to operate the OCT probe 600, and the connector 610. 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 (not shown) that is a solid-state imaging device is disposed in the back of the observation optical system 150. A signal cable (not shown) is connected to the substrate of the CCD, and this signal cable is inserted into the insertion portion 114, the hand operation portion 112, the universal cable 116, etc., 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 and converted into an electric signal. The 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 a resin.

  Note that the internal configurations of the endoscope, the endoscope processor, and the light source device are well-known and will not be described.

  FIG. 2 is a block diagram showing an internal configuration of the OCT processor of FIG.

  An OCT processor 400 and an OCT probe 600 shown in FIG. 2 are for obtaining an optical tomographic image of a measurement object by an optical coherence tomography (OCT) measurement method, and emit a light La for measurement. One light source unit (first light source unit) 12 and light La emitted from the first light source unit 12 are branched into measurement light (first light beam) L1 and reference light L2, and measurement is performed on the subject. An optical fiber coupler (branching / combining unit) 14 that generates the interference light L4 by combining the return light L3 from the target S and the reference light L2, and the measurement light L1 branched by the optical fiber coupler 14 is guided to the measurement target. And an OCT probe 600 including a rotation-side optical fiber FB1 that guides the return light L3 from the measurement target, and guides the measurement light L1 to the rotation-side optical fiber FB1 and rotates the rotation-side optical fiber. The fixed side optical fiber FB2 that guides the return light L3 guided by the bar FB1 and the rotation side optical fiber FB1 are rotatably connected to the fixed side optical fiber FB2, and the measurement light L1 and the return light L3 are transmitted. The optical connector 18, the interference light detection unit 20 that detects the interference light L 4 generated by the optical fiber coupler 14 as an interference signal, and the interference signal detected by the interference light detection unit 20 to process the optical tomographic image ( Hereinafter, the signal processing unit 22 is also obtained. Further, the optical tomographic image acquired by the signal processing unit 22 is displayed on the monitor device 500.

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

  In the OCT processor 400 shown in FIG. 2, 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 unit 12 emits light for OCT measurement (for example, laser light having a wavelength of 1.3 μm or low coherence light), and 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 unit 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 optical connector. 18 is input.

  The second light source unit 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 unit 13 includes, for example, a semiconductor laser 13a that emits red, blue, or green laser light, and a lens 13b that condenses the aiming light Le emitted from the semiconductor laser 13a. The aiming light Le emitted from the second light source unit 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 divides the light La incident from the first light source unit 12 via the optical fibers FB4 and FB3 into measurement light (first light flux) L1 and reference light L2, and the measurement light L1 is fixed. The light is incident on the optical 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 generates an interference signal based on the detection results of the detectors 30a and 30b.

  From the interference signal extracted by the interference light detection unit 20, the signal 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. An area in which the surface of the measurement object S can be considered to be in contact with the surface of the measuring object S, a tomographic image is acquired from the interference signal detected by the interference light detection unit 20, and the acquired tomographic image is output to the monitor device 500 To do.

  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 signal processing unit 22. The operation control unit 32 inputs, sets, and changes various processing conditions and the like in the signal 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. Further, the operation control unit 32 controls the operation of the first light source unit 12, the second light source unit 13, the optical connector 18, the interference light detection unit 20, the optical path length, the detectors 30a and 30b, and sets various conditions. You may do it.

  Next, the OCT probe 600 of this embodiment will be described.

  FIG. 3 is a perspective view schematically showing the tip of the OCT probe of FIG. 4 is a side sectional view of the OCT probe of FIG. 3 viewed from a direction parallel to the axial direction, and FIG. 5 is a front sectional view of the OCT probe of FIG. 3 viewed from a direction perpendicular to the axial direction.

  As shown in FIGS. 3 to 5, the distal end portion of the OCT probe 600 mainly includes a multi-lumen type sheath (probe outer tube) 620 having first and second lumens 630 and 632, and a rotation-side optical fiber FB1. And an optical lens 628.

  The sheath 620 has a structure in which two flexible tubular members (cylindrical members) are bonded in parallel by shifting the position of the tip in the axial direction, and the first lumen is attached to one tubular member. 630 is formed, and the second lumen 632 is formed on the other tubular member.

  The first and second lumens 630 and 632 are juxtaposed so as to be parallel to each other, and the first lumen 630 has a predetermined tip protrusion amount X (see FIG. 4) closer to the tip end in the axial direction than the second lumen 632. (See)). The projecting portion of the first lumen 630 (the portion projecting toward the tip end side in the axial direction from the second lumen 632) 630a is formed in a cylindrical shape, and the wall thickness of the outer peripheral wall is uniform along the circumferential direction and the axial direction. It is configured.

  The sheath 620 is made of a material (light transmissive material) that transmits the measurement light L1 (aiming light Le) and the return light L3. Note that it is not always necessary that the entire sheath 620 is made of a light transmissive material, and at least the outer peripheral wall of the protruding portion 630a of the first lumen 630 may be made of a light transmissive material.

  The first lumen 630 is a probe body insertion channel (pipe) through which probe bodies such as the rotation side optical fiber FB1 and the optical lens 628 are inserted. The distal end of the first lumen 630 is configured to be blocked for the purpose of preventing intrusion of body fluid, cleaning fluid, and the like, and is blocked by, for example, a cap (not shown).

  The rotation-side optical fiber FB1 is a linear member, and is accommodated in the first lumen 630 along the axial direction of the first lumen 630. From the fixed-side optical fiber FB2 via the optical connector 18 The incident measurement light L1 (aiming light Le) is guided to the optical lens 628, and the return light L3 from the measurement target S acquired by the optical lens 628 is guided to the optical connector 18.

  Here, the rotation side optical fiber FB1 and the fixed side optical fiber FB2 are connected by the optical connector 18 as shown in FIG. 2, and the rotation of the rotation side optical fiber FB1 is not transmitted to the fixed side optical fiber FB2. , Optically connected. Further, the rotation-side optical fiber FB1 is arranged so as to be rotatable about its axial direction and movable along the axial direction of the rotation-side optical fiber FB1.

  The optical lens 628 is disposed at the measurement-side tip of the rotation-side optical fiber FB1 (tip of the rotation-side optical fiber FB1 opposite to the optical connector 18), and the measurement light L1 guided by the rotation-side optical fiber FB1 ( In order to collect the aiming light Le) with respect to the measuring object S, it is formed in a substantially spherical shape.

  The optical lens 628 irradiates the measurement object S with the measurement light L1 (aiming light Le) transmitted from the rotation side optical fiber FB1, collects the return light L3 from the measurement object S, and transmits it to the rotation side optical fiber FB1. To do.

  The rotation-side optical fiber FB1 and the optical lens 628 are configured to be rotatable in the arrow R2 direction around the axial direction of the rotation-side optical fiber FB1 by the drive unit 640 (see FIG. 4), and are parallel to the axial direction. It is configured to be movable in the arrow S1 direction (forceps opening direction) and the S2 direction (front end direction of the first lumen 630). In addition, since the structure of the drive part 640 is known, description is abbreviate | omitted here.

  The second lumen 632 is a treatment instrument insertion channel (pipe) through which a treatment instrument for performing a biopsy or treatment is inserted. Here, as an example, a biopsy brush 634 as a treatment tool is inserted through the second lumen 632. Note that the treatment instrument inserted through the second lumen 632 is not limited to the biopsy brush 634, and for example, a radiation marker, a high-frequency marker, or the like may be used.

  An opening 632 a is formed at the tip of the second lumen 632. By deriving the brush portion 634a formed at the tip of the biopsy brush 634 through the opening 632a, the biopsy of the measurement target S can be performed while observing the tomographic image by the OCT probe 600. On the other hand, when it is not necessary to perform a biopsy (that is, when only a tomographic image is observed), the brush portion 634a of the biopsy brush 634 is located inside the opening 632a, that is, in the second lumen 632. The biopsy brush 634 is completely accommodated. Further, after the biopsy is completed, the biopsy brush 634 is accommodated in the second lumen 632, so that the tip of the OCT probe 600 is pulled out of the subject as a protective part of the biopsy brush 634. Also works.

  The second lumen 632 is provided with a stopper portion 636 for restricting the protruding amount of the treatment instrument such as the biopsy brush 634. The stopper portion 636 is formed at a predetermined position on the inner peripheral surface of the second lumen 632 so as to protrude inward over the entire circumferential direction or a part thereof. A stopper portion 638 is provided on the shaft portion 634 b of the biopsy brush 634, and the opening portion of the second lumen 632 is brought into contact with the stopper portion 636 of the second lumen 632. The protruding amount of the biopsy brush 634 from 632a is regulated. The same applies to the case where a radiation marker, a high-frequency marker, or the like is used as a treatment instrument.

  In this embodiment, when the distal end portion of the OCT probe 600 led out from the forceps port 156 of the endoscope 100 is pressed against the measurement target S, the second lumen 632 side is not the first lumen 630 side but the measurement target S. To face each other. At this time, the focal length f of the optical lens 628 is preferably set according to the diameter of the second lumen 632.

  By pressing the tip of the OCT probe 600 against the measuring object S so that the second lumen 632 side faces the measuring object S instead of the first lumen 630 side, the optical lens 628 and the measuring object S are not connected to each other. A constant distance according to the diameter of the second lumen 632 is maintained. Therefore, by setting the focal length f of the optical lens 628 according to the diameter of the second lumen 632, the focal point of the optical lens 628 can be easily measured by simply pressing the OCT probe 600 against the measurement target S. S can be matched. Thereby, the detection accuracy of the return light L3 from the measuring object S can be improved.

  The sheath 620 is preferably provided with a probe orientation detection marker 642 for detecting the orientation of the OCT probe 600. Specifically, a linear probe orientation detection marker 642 extending in the axial direction is formed at a position 180 degrees opposite to the second lumen 632 in the outer peripheral wall of the first lumen 630. In this example, the probe orientation detection marker 642 is formed on the outer side of the outer peripheral wall of the first lumen 630. However, the present invention is not limited to this, and may be formed on the inner side of the outer peripheral wall of the first lumen 630. Thus, when the tip of the OCT probe 600 is pressed against the measuring object S, the operator can easily identify the orientation of the OCT probe 600 by confirming the probe orientation detection marker 642 that appears in the tomographic image. Is possible.

  Next, the operation of the OCT probe 600 of this embodiment will be described.

  First, the OCT probe 600 is inserted from the forceps insertion portion 138 provided in the hand operation portion 112 of the endoscope 100, and the OCT probe 600 is led out from the forceps opening 156. Then, the tip of the OCT probe 600 led out from the forceps port 156 of the endoscope 100 is pressed against the measurement object S. At that time, not the first lumen 630 side but the second lumen 632 side faces the measuring object S.

  The OCT probe 600 uses the drive unit 640 to rotate the rotation-side optical fiber FB1 and the optical lens 628 in the direction of the arrow R2, so that the measurement light L1 (aiming light Le) emitted from the optical lens 628 becomes the measurement target S. On the other hand, irradiation is performed while scanning in the direction of the arrow R2, and the return light L3 from the measurement target S is acquired. The aiming light Le is irradiated to the measuring object S as, for example, blue, red, or green spot light, and the reflected light of the aiming light Le is also displayed as a bright spot on the observation image displayed on the monitor device 500.

  Thereby, the desired site | part of the measuring object S can be caught correctly in the perimeter of the circumferential direction of the 1st lumen | rumen 630, and the return light L3 which reflected the measuring object S can be acquired.

  Further, when acquiring a plurality of tomographic images for generating three-dimensional volume data, the optical lens 628 is moved by the drive unit 640 to the end of the movable range in the arrow S1 direction (point A in FIG. 3), The image is moved in the S2 direction by a predetermined amount while acquiring the image, or is moved to the end of the movable range (point B in FIG. 3) while alternately repeating the tomographic image acquisition and the predetermined amount movement in the S2 direction. Note that the movable range of the optical lens 628 (the range from the point A to the point B in FIG. 3) is included in the protrusion 630 a of the first lumen 630.

  Thus, a plurality of tomographic images in a desired range can be obtained for the measurement object S, and three-dimensional volume data can be obtained based on the acquired plurality of tomographic images.

  When performing biopsy of the measuring object S using the biopsy brush 634, the brush portion 634a of the biopsy brush 634 is derived from the opening 632a of the second lumen 632, and the position of the brush portion 634a is determined. While confirming the tomographic image displayed on the monitor device 500, the image is brought closer to the measuring object S. And the structure | tissue of the measuring object S is extract | collected by rubbing the surface of the measuring object S with the brush part 634a of the biopsy brush 634. FIG.

  After the biopsy is thus completed, the biopsy brush 634 is accommodated in the second lumen 632. Thereby, it is possible to protect the tissue attached to the surface of the biopsy brush 634 until the tip of the OCT probe 600 is pulled out of the subject.

  In the OCT probe 600 of the present embodiment, the movable range of the optical lens 628 (the range from the point A to the point B in FIG. 4) is the front end side of the protruding portion of the first lumen 630 (the second lumen 632). (Projected portion) 630a, and the outer peripheral wall of the projecting portion 630a of the first lumen 630 is configured in a cylindrical shape, and the wall thickness thereof is configured uniformly in the circumferential direction and the axial direction. The Therefore, when acquiring the return light L3 from the measurement target S while scanning the measurement light L1 irradiated to the measurement target S from the optical lens 628, the refraction of the light passing through the sheath 620 depending on the scanning direction of the measurement light L1. The influence (degree) is not different, the interference light detection accuracy is improved, and a good tomographic image can be obtained. This makes it possible to perform biopsy or treatment while confirming the position of the lesion site from the optical tomographic image even in a lesion site in a narrow region in the body cavity that cannot be observed by the endoscope.

  FIG. 6 is a front cross-sectional view showing another configuration example of the tip of the OCT probe. In the figure, a cross section corresponding to the base end side from the cross section shown in FIG. 5 is shown. In FIG. 6, members that are the same as those in FIG.

  The first to third fixing balloons 644A, 644B, and 644C are provided on the outer peripheral surface of the first lumen 630 (the outer surface of the outer peripheral wall) at the distal end portion of the OCT probe 600 shown in FIG. Specifically, the outer peripheral surface of the second lumen 632 is disposed on the outer peripheral surface of the first lumen 630 on the proximal end side with respect to the protruding portion (the portion protruding toward the distal end side in the axial direction from the second lumen 632). The fixing balloons 644A to 644C are arranged while shifting the phase by 90 degrees starting from the position where the (outer surface of the outer peripheral wall) is connected. Although illustration is omitted, inside the first lumen 630, gas supply conduits communicating with the respective fixing balloons 644A to 644C are provided, and each of the fixing balloons 644A to 644C is a gas supply tube. It is configured to be freely expandable and contractible by gas supplied or sucked through the passage. Here, a configuration in which three fixing balloons 644A to 644C are arranged as a preferred embodiment is shown. However, the present invention is not limited to this. For example, one or two fixing balloons may be arranged, and four or more balloons may be arranged. The fixing balloon may be arranged.

  According to the configuration shown in FIG. 6, when the distal end portion of the OCT probe 600 led out from the forceps port 156 of the endoscope 100 is pressed against the measuring object S, the fixing balloons 644A to 644C are expanded from the contracted state to the expanded state. The surface of each of the fixing balloons 644A to 644C is brought into contact with the body cavity wall of the subject. Thereby, since the front-end | tip part of the OCT probe 600 is fixed in a desired position, it becomes possible to acquire a favorable tomographic image with the OCT probe 600 in a stable state.

  In the above-described embodiment, the SS-OCT (Swept Source OCT) apparatus is described as the OCT processor 400. However, the present invention is not limited to this, and the OCT processor 400 can also be applied as an SD-OCT (Spectral Domain OCT) apparatus. It is.

  Although the optical probe and the optical tomographic imaging 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.

  DESCRIPTION OF SYMBOLS 10 ... Diagnostic imaging apparatus, 22 ... Signal processing part, 100 ... Endoscope, 156 ... Forceps opening, 200 ... Endoscope processor, 300 ... Light source apparatus, 400 ... OCT processor, 500 ... Monitor apparatus, 600 ... OCT probe, 620 ... sheath, 630 ... first lumen, 632 ... second lumen, 634 ... biopsy brush, 636 ... stopper member, 638 ... stopper receiving portion, 640 ... driving portion, 644A, 644B, 644C ... balloon for fixation

Claims (11)

The measurement light, which is in the sheath inserted into the subject and propagates through the optical fiber from the light source, is irradiated to the measurement object while rotating and scanning around the axis of the optical fiber, and the return light from the measurement object is received. In an optical probe provided with an optical system introduced into the optical fiber,
A first lumen in which the distal end portion is closed and the optical system is accommodated, and a second lumen in which an opening is formed in the distal end portion and a treatment tool for performing biopsy or treatment is accommodated. With a sheath
The first and second lumens are arranged side by side so that the axial directions of the first and second lumens are parallel to each other, and the first lumen is formed so as to protrude toward the distal end side in the axial direction from the second lumen.
The optical system is disposed in a protruding portion of the first lumen that protrudes from the second lumen, and an outer wall of the protruding portion is made of a light-transmitting member and has a uniform thickness. An optical probe characterized by being configured in a cylindrical shape. The focal length of the optical system is determined according to the diameter of the second lumen,
2. The optical probe according to claim 1, wherein the optical probe is pushed so that the second lumen side of the first and second lumens is a measurement target side. The second lumen is provided with a stopper member for restricting the amount of projection of the treatment instrument led out from the opening,
3. The optical probe according to claim 1, wherein the amount of protrusion of the treatment instrument is regulated by bringing a stopper receiving portion provided in the treatment instrument into contact with the stopper member.   The optical probe according to any one of claims 1 to 3, wherein the sheath is provided with marker means for identifying the orientation of the first or second lumen.   The optical probe according to claim 4, wherein the marker means is provided on an outer wall of the first lumen opposite to the second lumen. The sheath comprises at least one anchoring balloon;
6. The optical probe is fixed by bringing the fixing balloon into contact with a body cavity wall in a subject when the optical probe is pressed against a measurement target. The optical probe according to 1.   The optical probe according to claim 1, wherein the treatment tool is a biopsy brush.   The optical probe according to any one of claims 1 to 6, wherein the treatment instrument is a radiation marker or a high-frequency marker. The optical system scans the measurement light applied to the measurement object while rotating in the axial direction of the optical fiber while rotating around the axis of the optical fiber,
The optical probe according to any one of claims 1 to 8, wherein the movable range of the optical system in the axial direction is included in the protruding portion.   The optical probe according to any one of claims 1 to 9, wherein the sheath has a structure in which tips of two tubular members are bonded in parallel while being shifted in the axial direction. A light splitting means for splitting light emitted from the light source into measurement light and reference light;
Irradiation optical means for irradiating the measurement light to the measurement object;
Multiplexing means for multiplexing the reflected light from the measurement object by the measurement light irradiated by the irradiation optical means and the reference light;
Interference light detection means for detecting interference light between the reflected light and the reference light multiplexed by the multiplexing means;
Image acquisition means for acquiring a tomographic image of the measurement object based on the interference light detected by the interference light detection means;
Have
An optical tomographic imaging apparatus comprising the optical probe according to any one of claims 1 to 10, wherein the irradiation optical means includes the optical probe according to any one of claims 1 to 10.

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