JP5105558B2 - Optical probe and optical tomographic imaging apparatus - Google Patents

Description

  The present invention relates to an optical probe, and more particularly to an optical probe having a cylindrical probe outer cylinder and having a function of deflecting light emitted from the peripheral surface thereof in the circumferential direction of the outer cylinder.

  The present invention also relates to an optical tomographic imaging apparatus using the optical probe as described above.

  Conventionally, as one method for acquiring a tomographic image of a measurement target such as a living tissue, for example, as shown in Patent Documents 1 and 2, a method for acquiring an optical tomographic image by OCT (Optical Coherence Tomography) measurement has been proposed. ing. This OCT measurement is a kind of optical interference measurement, and optical interference is detected only when the optical path length of the light divided into two, that is, the measurement light and the reference light is within a range within the coherence length of the light source. This is a measurement method using this. 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 the reflected light from the measurement object is guided to the multiplexing means. On the other hand, the optical path length of the reference light is adjusted so that the optical path length is the same as the reflected light from an arbitrary place to be measured in the measurement target, and the reference light is guided to the multiplexing means. Then, the measuring light and the reference light are combined by the combining means, and the light intensity is detected by the photodetector.

  In order to obtain a one-dimensional tomographic image, the optical path length of the measurement light is scanned according to the measurement area, and an interference intensity waveform corresponding to the reflectance distribution along the same axis as the measurement light traveling direction is obtained. It is done. That is, a light reflection intensity distribution according to the structure in the depth direction of the measurement target can be obtained. Furthermore, a tomographic image of a two-dimensional light reflection intensity is obtained by scanning the irradiation position of the measurement light applied to the measurement object in a one-dimensional direction perpendicular to the optical axis using a deflection means or a physical movement means. It is done. Furthermore, a tomographic image having a three-dimensional light reflection intensity can be obtained by scanning the irradiation position of the measurement light over a two-dimensional direction perpendicular to the optical axis direction.

  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. More specifically, the optical path length adjustment mechanism of the reference light in Patent Document 1 has an optical system that focuses the reference light emitted from the optical fiber onto the mirror, and moves only the mirror in the beam axis direction of the reference light. The optical path length is adjusted. The optical path length adjustment mechanism for the reference light shown in Patent Document 2 collimates the reference light emitted from the optical fiber by the lens, and condenses the reference light that has become parallel light again by the optical path length adjustment lens. The light is incident on the fiber, and the optical path length is adjusted by advancing and retracting the optical path length adjusting lens in the beam axis direction of the reference light.

  On the other hand, an optical tomographic imaging apparatus based on SD-OCT (Spectral Domain OCT) measurement has been proposed as an apparatus for acquiring a tomographic image at high speed without changing the optical path length of the reference light described above. In the SD-OCT apparatus, as in the above TD-OCT, a broadband low-coherent light divided into a measurement light and a reference light using an interferometer is caused to interfere with the optical path length being almost equal, and then the interference light is spectrally separated. By measuring the interference light intensity for each optical frequency component with an array type photodetector, and analyzing the resulting spectrum interference waveform with a Fourier transform using a computer. Thus, a one-dimensional tomographic image in the optical axis direction is constructed without physically performing the above scanning. Similar to the TD-OCT, a two-dimensional or three-dimensional tomographic image can be obtained by scanning the irradiation position of the measurement light in a direction perpendicular to the optical axis.

  Furthermore, an optical tomographic imaging apparatus based on SS-OCT (Swept source OCT) measurement has been proposed as an apparatus for acquiring a tomographic image at high speed without changing the optical path length of the reference light. This SS-OCT apparatus uses an optical frequency variable laser light source as a light source. The high coherence laser light 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 interfering with the measurement light and the optical path length approximately equal to each other. Then, the measuring light and the reference light are combined by the combining means, and the light intensity is detected by the photodetector. By scanning the frequency of the optical frequency variable laser light source, the interference light intensity for each optical frequency component is measured, and the spectral interference waveform obtained here is Fourier transformed by a computer to physically scan the optical path length. In this way, a one-dimensional tomographic image in the optical axis direction is constructed. Similar to the TD-OCT, a two-dimensional or three-dimensional tomographic image can be obtained by scanning the irradiation position of the measurement light in a direction perpendicular to the optical axis.

  In each type of optical tomographic imaging apparatus as described above, a tomographic image along a certain surface of the measurement target is usually acquired. For this purpose, at least the measurement light is used as the optical axis in the measurement target. It is necessary to scan in a vertical one-dimensional direction. As one of means for performing such optical scanning, conventionally, as shown in Patent Document 3, a cylindrical probe outer cylinder is provided, and light emitted from the peripheral surface of the outer cylinder is along the peripheral surface. An optical probe having a function of deflecting in a different direction is known. More specifically, the optical probe includes an insertion portion (probe outer cylinder) to be inserted into the subject, a rotatable hollow shaft inserted into the inner space of the probe outer cylinder, and the shaft. And an optical deflection element that is fixed to the tip of the shaft and rotates together with the shaft and deflects light emitted from the tip of the optical fiber in a direction around the peripheral surface of the probe outer cylinder.

JP-A-6-165784 JP 2003-139688 A Japanese Patent No. 3104984

  Observation of optical tomographic images is expected to expand from bronchial, ureteral, and blood vessels to the finer areas from previously reported gastrointestinal organs. It is hoped to do. However, in the optical probe disclosed in Patent Document 3, it is necessary to form the shaft with a considerable thickness in order to ensure the strength of the shaft, and a gap is secured between the shaft and the internal optical fiber. Therefore, miniaturization is difficult.

  In addition, there is a demand for observing deeper areas in the subject, and in that case, it is necessary to make a long probe as long as several meters, but the work of passing an optical fiber through a fine and long cylindrical shaft Is very difficult. In addition, since the optical fiber may be broken when it is inserted into the shaft, such an optical probe has poor productivity. Furthermore, the production of such a cylindrical shaft is costly, which increases the cost of the optical probe.

  The present invention has been made in view of the above circumstances, and an object thereof is to provide an optical probe that can be easily reduced in diameter and can be manufactured at low cost.

  Another object of the present invention is to provide an optical tomographic imaging apparatus that can be reduced in size and cost by using such an optical probe.

  The optical probe according to the present invention rotates the optical deflecting element into the probe outer cylinder while avoiding a complicated configuration of inserting a hollow shaft into the probe outer cylinder and further inserting an optical fiber into the shaft. Therefore, the above-mentioned object is achieved by arranging the supporting member and the optical fiber side by side.

That is, more specifically, the optical probe according to the present invention is:
A cylindrical probe outer tube,
A support member disposed in an inner space of the probe outer cylinder so as to extend in an axial direction of the outer cylinder;
A plurality of optical fibers that extend alongside the support member in the internal space of the probe outer cylinder and are disposed in a state in which the central axis is deviated from the rotation center of the support member, and are supported by the support member ; ,
Drive means connected to the base end side of the support member and rotating the support member in the circumferential direction of the outer cylinder;
A light deflection element that rotates together with the support member and deflects the light emitted from the tip of the optical fiber in the circumferential direction of the outer cylinder;
Condensing means for condensing the light emitted from the tip of the optical fiber and converging it in a scanned object disposed on the outer periphery of the probe outer cylinder;
Light guide means is provided for guiding the light reflected by the scanned object to the tip of the optical fiber and causing the light to enter the optical fiber from the tip.

Note In the optical probe of the present invention having the above structure, since the supporting member and the optical fiber are integrated, so that the optical fiber rotates together with the support member.

Also, before Symbol probe sheath tip portion, it is desirable that a bearing part for nest rotatably the rotation shaft of the supporting member is disposed.

On the other hand, the optical tomographic imaging apparatus according to the present invention is characterized in that the optical probe according to the present invention is used in the optical tomographic imaging apparatus of each measurement method as described above. That is, the optical tomographic imaging apparatus according to the present invention more specifically,
A light source that emits light;
A light splitting means for splitting light emitted from the light source into measurement light and reference light;
An irradiation optical system for irradiating the measurement object with the measurement light;
A multiplexing means for multiplexing the reflected light from the measurement object and the reference light when the measurement object is irradiated with the measurement light;
Interference light detection means for detecting interference light between the reflected light and the reference light combined;
Based on the detected frequency and intensity of the interference light, the intensity of the reflected light at a plurality of depth positions of the measurement object is detected, and the tomography of the measurement object is detected based on the intensity of the reflected light at each depth position. In an optical tomographic imaging apparatus comprising an image acquisition means for acquiring an image,
The irradiation optical system includes an optical probe according to the present invention.

  In the optical probe of the present invention, the support member and the optical fiber are arranged side by side in the probe outer cylinder, and the optical deflection element is rotated by rotating the support member. Compared with the conventional optical probe in which the shaft is inserted and the optical fiber is inserted into the shaft, the structure becomes extremely simple. Therefore, this optical probe can be easily reduced in diameter and can be manufactured at low cost.

  Furthermore, since the optical probe according to the present invention has the support member and the optical fiber arranged side by side in the probe outer cylinder, the combination and fixing of the support member and the optical fiber can be performed even when the overall length is considerably long. This is not very difficult, and thus the manufacturing cost can be kept low also in this respect.

In the optical probe of the present invention, in particular,
The optical fiber is supported by the support member with its central axis deviating from the rotation center of the support member,
When a bearing portion that rotatably receives the rotation shaft of the support member is disposed in the distal end portion of the probe outer cylinder,
The probe diameter can be further reduced by rotating the optical fiber around the rotation axis deviated from the fiber central axis in the probe outer cylinder.

  On the other hand, since the optical tomographic imaging apparatus according to the present invention is applied with the optical probe according to the present invention as described above, it is possible to realize downsizing and cost reduction.

1 is a side sectional view showing an optical probe according to a first embodiment of the present invention. Elevated cross-sectional view of the optical probe of FIG. 1 is an overall perspective view of an optical tomographic imaging apparatus to which the optical probe of FIG. 1 is applied. Side sectional view showing an optical probe according to a second embodiment of the present invention. Fig. 4 is an elevational sectional view of the optical probe of Fig. 4 Sectional drawing which shows the optical probe by 3rd Embodiment of this invention Sectional drawing which shows the optical probe by 4th Embodiment of this invention Side sectional view showing an optical probe according to a fifth embodiment of the present invention. Elevated sectional view of the optical probe of FIG. Side sectional view showing an optical probe according to a sixth embodiment of the present invention. Schematic configuration diagram showing an example of an optical tomographic imaging apparatus by SD-OCT measurement using the optical probe of the present invention Schematic configuration diagram showing an example of an optical tomographic imaging apparatus using SS-OCT measurement using the optical probe of the present invention Schematic configuration diagram showing an example of an optical tomographic imaging apparatus based on TD-OCT measurement using the optical probe of the present invention

  Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. FIG. 1 shows a side cross-sectional shape of an optical probe 10 according to the first embodiment of the present invention, and FIG. 2 shows the optical probe 10 cut away at the position of line AA in FIG. FIG. The optical probe 10 constitutes, for example, a distal end portion of an endoscope that is a part of the optical tomographic imaging apparatus, and FIG. 3 shows the overall shape of the optical tomographic imaging apparatus.

  First, an outline of the optical tomographic imaging apparatus will be described with reference to FIG. This apparatus includes an endoscope 50 including the optical probe 10, a light source device 51, a video processor 52 and an optical tomography processing device 53 to which the endoscope 50 is connected, and a monitor 54 connected to the video processor 52. I have. The endoscope 50 includes an elongated probe outer tube 11 having flexibility, an operation unit 56 connected to the rear end of the probe outer tube 11, and a universal extending from a side portion of the operation unit 56. Code 57 is provided.

  A light guide (not shown) that transmits illumination light from the light source device 51 is inserted into the universal cord 57, and a light source connector that is detachably connected to the light source device 51 at the end of the universal cord 57 58 is provided. A signal cable 59 extends from the light source connector 58, and a signal connector 60 that is detachably connected to the video processor 52 is provided at an end of the signal cable 59. The light source device 51 is for irradiating illumination light to a portion of the subject 70 from which a tomographic image is acquired as described later.

  The operation section 56 is provided with a bending operation knob 61 for bending the bending section provided on the probe outer cylinder 11, and a light guide driving section 62. The light guide driving section 62 and the optical tomography are provided. A processing device 53 is connected via a ride guide 63. The probe outer cylinder 11 is inserted into a subject 70 such as a human organ.

  Next, the optical probe 10 will be described with reference to FIGS. The optical probe 10 includes a cylindrical probe outer cylinder 11 with a closed tip, a support member 12 disposed in an inner space of the probe outer cylinder 11 and extending in the axial direction of the outer cylinder 11, In the inner space of the probe outer cylinder 11, one optical fiber 13 arranged so as to extend side by side with the support member 12 and the support member 12 connected to the proximal end side of the support member 12 are connected to the probe outer cylinder. 11 and a motor 14 that rotates in the circumferential direction.

  The optical fiber 13 is fixed to the support member 12 by a fiber fixing member 15. A disk-like bearing 16 having a through hole at the center is fixed inside the probe outer cylinder 11 at a position close to the tip. The distal end portion of the support member 12 is formed in an L-shape, and the distal end portion is inserted into the through hole of the bearing 16 so that the support member 12 is rotated around the central axis (longitudinal axis) of the probe outer cylinder 11. It is free to rotate. Therefore, when the motor 14 is driven, the support member 12 rotates with the optical fiber 13.

  Further, the optical probe 10 is supported by the support member 12 and rotates together with the support member 12, and a prism mirror 17 that deflects the light L emitted from the tip of the optical fiber 13 in the circumferential direction of the probe outer cylinder 11, It has a rod lens 18 that condenses the light L emitted from the tip of the fiber 13 so as to converge on a subject 70 as a scanning body disposed on the outer periphery of the probe outer cylinder 11. In this embodiment, as will be described later, the rod lens 18 and the prism mirror 17 guide light L reflected by the subject 70 to the tip of the optical fiber 13 and enter the optical fiber 13 from the tip. Doubles as

  A portion near the base end of the optical fiber 13 is bent so as to bypass the motor 14, and the base end is arranged coaxially with the rotation axis of the support member 12. As shown in FIG. 3, an incident optical system 20 is disposed inside the endoscope 50 so as to face the proximal end of the optical fiber 13. Light L guided through the ride guide 63 and emitted therefrom is collected by the incident optical system 20 and enters the optical fiber 13 from the base end.

  Hereinafter, the operation of the optical probe 10 having the above configuration will be described. A light source (not shown) such as a laser is disposed in the optical tomography processing device 53 shown in FIG. 3, and light L such as laser light emitted from the light tomography enters the ride guide 63 and is guided there. After being emitted from the ride guide 63, the light L incident on the optical fiber 13 through the incident optical system 20 is guided through the optical fiber 13, emitted from the tip, and condensed by the rod lens 18, and then the prism mirror 17. And the light path is changed by 90 ° and emitted from the translucent probe outer cylinder 11 to the outside of the probe. When the motor 14 is driven, the support member 12 rotates as described above, and the optical fiber 13, the prism mirror 17, and the rod lens 18 fixed to the support member 12 also rotate together with the support member 12.

  When the prism mirror 17 rotates as described above, the light L emitted therefrom is deflected in the circumferential direction of the probe outer cylinder 11 and scans the subject 70 in the direction of arrow R in FIG. The light L is reflected while being scattered by the subject 70, and a part of the reflected light enters the prism mirror 17 and is reflected toward the rod lens 18 side. The reflected light is collected by the rod lens 18 and enters the optical fiber 13 from the tip of the optical fiber 13.

  The reflected light propagating in the optical fiber 13 is emitted from the base end of the optical fiber 13 and enters the ride guide 63 through the incident optical system 20, and is guided through the ride guide 63 to the optical tomography processing device 53. Light is transmitted. In the optical tomography processing device 53, the reflected light is branched from the optical path of the light L toward the optical probe 10 and is detected by a photodetector (not shown). Based on the output of the photodetector, a tomographic image of the subject 70 is formed, and this tomographic image is displayed on the monitor 54 shown in FIG.

  As described above, in the optical probe 10 of the present embodiment, the support member 12 and the optical fiber 13 are arranged side by side in the probe outer cylinder 11, and the prism mirror 17 as an optical deflection element is rotated by rotating the support member 12. Since the rotation is made, the structure is very simple as compared with a conventional optical probe having a structure in which a hollow shaft is inserted into the probe outer tube and an optical fiber is inserted into the shaft. Therefore, the optical probe 10 can be easily reduced in diameter and can be manufactured at low cost.

  Furthermore, since the optical probe 10 of the present embodiment has the support member 12 and the optical fiber 13 arranged side by side in the probe outer cylinder 11, the support member 12 and the optical fiber 13 can be formed even when the overall length is considerably long. It is possible to keep the manufacturing cost low from this point of view.

  In the present embodiment, the optical fiber 13 is supported by the support member 12 with its central axis deviating from the rotation center of the support member 12, so that the optical fiber 13 is within the probe outer cylinder 11, It rotates around a rotation axis deviated from the fiber central axis. In this case, as is apparent from FIG. 2, it is only necessary to secure the inner diameter of the probe outer cylinder 11 by (the outer diameter of the optical fiber 13) + (the vertical dimension of the support member 12). On the other hand, when the support member is cylindrical and the optical fiber disposed coaxially therein is rotated, if the thickness of the cylindrical support member is the same as the vertical dimension, the probe outer cylinder The inner diameter of 11 is only required (the outer diameter of the optical fiber 13) + (the longitudinal dimension of the support member × 2), and the probe outer cylinder 11 becomes thicker.

  Next, a second embodiment of the present invention will be described. FIG. 4 shows a side cross-sectional shape of the optical probe 100 according to the second embodiment of the present invention, and FIG. 5 shows the optical probe 100 broken at the position of line BB in FIG. FIG. 4 and 5, the same elements as those in FIGS. 1 to 3 are denoted by the same reference numerals, and description thereof will be omitted unless necessary (the same applies hereinafter).

  Compared with the optical probe 10 of the first embodiment described above, the optical probe 100 of the second embodiment is provided with two support members 12 with the optical fiber 13 sandwiched therebetween, and these support members The point that 12 is rotatable within the annular bearing 30 is different, and the other points are basically configured in the same manner.

  Next, a third embodiment of the present invention will be described. FIG. 6 shows an elevational cross-sectional shape of an optical probe 110 according to the third embodiment of the present invention. Compared with the optical probe 10 of the first embodiment described above, the optical probe 110 of the third embodiment is provided with three support members 12 with the optical fiber 13 sandwiched therebetween, and these support members The bearing for receiving 12 is different in that it is not provided. In other words, in the present embodiment, the inner diameter of the probe outer cylinder 11 is sized so that a slight gap is formed between the three support members 12, and these support members 12 slide with the inner surface of the peripheral wall of the probe outer cylinder 11. While rotating.

  Although not specifically shown, the optical fiber 13 is fixed to the three support members 12 by a fixing member similar to the fiber fixing member 15 shown in FIGS. The three support members 12 are preferably arranged at equiangular intervals around the axis of the optical fiber 13, but may be arranged at unequal angular intervals without doing so.

  Next, a fourth embodiment of the present invention will be described. FIG. 7 shows a vertical sectional shape of an optical probe 120 according to the fourth embodiment of the present invention. The optical probe 120 of the fourth embodiment is provided with two support members 12 as compared with the optical probe 110 of the third embodiment described above, and the support member 12 and the optical fiber 13 are supported. The difference is that the members 12 are integrated by the covering material 31 extending over substantially the entire length. In other words, in the present embodiment, the inner diameter of the probe outer cylinder 11 is sized so that a slight gap is formed between the probe outer cylinder 11 and the covering material 31 so that it rotates while sliding on the inner surface of the peripheral wall of the probe outer cylinder 11. It has become.

  Next, a fifth embodiment of the present invention will be described. FIG. 8 and FIG. 9 show the side sectional shape and the vertical sectional shape of the optical probe 130 according to the fifth embodiment of the present invention, respectively. The optical probe 130 of the fifth embodiment is different from the optical probe 120 of the fourth embodiment described above in that two optical fibers 13 are provided. Correspondingly, two prism mirrors 17 and two rod lenses 18 are provided. In FIG. 8, the covering material 31 shown in FIG. 9 is omitted.

  In the optical probe 130 of the present embodiment, one optical fiber 13 is dedicated to light transmission, and the light emitted from the tip of the optical fiber 13 passes through the rod lens 18 and the prism mirror 17 in the same manner as described above (for example, FIG. 3 of the subject 70). That is, in this case, in FIG. 8, the light is emitted from one prism mirror 17 in a direction perpendicular to the paper surface.

  The light reflected by the object to be scanned enters a prism mirror 17 different from the above and is reflected there, and is collected by a rod lens 18 different from the above and is dedicated to light reception. Is incident on. This light propagates through the other optical fiber 13 and is sent to a predetermined light receiving section.

  Next, a sixth embodiment of the present invention will be described. FIG. 10 shows a side sectional shape of an optical probe 140 according to the sixth embodiment of the present invention. Compared with the optical probe 130 of the fifth embodiment described above, the optical probe 130 of the sixth embodiment is configured such that two optical fibers 13 serve as both light transmission and light reception. The point is different.

  In other words, in the present embodiment, the two prism mirrors 17 are disposed so that the directions are opposite to each other, and the light L is emitted in a state in which the directions are different from each other by 180 °. Then, the light L that has been emitted from one optical fiber 13 and reflected by the object to be scanned returns to the one optical fiber 13, and the light L that has been emitted from the other optical fiber 13 and reflected by the object to be scanned is The optical fiber 13 is returned to. By adopting such a configuration, it is possible to simultaneously perform optical scanning on different parts of the scanned object, or to perform optical scanning of the same part of the scanned object at a higher speed.

  Also in each of the optical probes of the second to sixth embodiments described above, one or a plurality of support members 12 and one or a plurality of optical fibers 13 are basically arranged in the probe outer cylinder 11 side by side. Since the support member 12 is rotated to rotate the prism mirror 17, the same effect as in the first embodiment can be obtained.

  The optical probe of each embodiment described above constitutes an endoscope that is a part of the optical tomographic imaging apparatus. However, the present invention is not limited to such an optical probe, and the outside of the cylindrical probe is used. The present invention is applicable to all optical probes that have a cylinder and deflect light emitted from the peripheral surface of the outer cylinder in the circumferential direction of the outer cylinder, and in any case, the effects described above can be achieved.

  In the embodiment described above, the light deflection element, the light condensing unit, and the optical fiber are arranged in close contact with each other. However, this is not always necessary, and they may be arranged apart from each other. . Further, the positions along the optical axis of the light deflection element and the condensing means may be reversed from those in the above-described embodiments so that the light deflection element is positioned on the light source side.

  Hereinafter, an example of an optical tomographic imaging apparatus to which the optical probe according to the present invention is applied will be described. First, an optical tomographic imaging apparatus 1 shown in FIG. 11 acquires a tomographic image of a measurement target such as a living tissue or a cell in a body cavity by the above-mentioned SD-OCT measurement, and a light source unit that emits light La. 210, light splitting means 3 for splitting the light La emitted from the light source unit 210 into measurement light L1 and reference light L2, and optical path length adjustment for adjusting the optical path length of the reference light L2 split by the light splitting means 3 Means 220, an optical probe 10 that irradiates the measuring object Sb with the measuring light L1 divided by the light dividing means 3, and thus the reflected light L3 reflected by the measuring object Sb when the measuring object Sb is irradiated with the measuring light L1. And the reference light L2, and the interference light detection means 240 for detecting the interference light L4 between the combined reflected light L3 and the reference light L2.

  The light source unit 210 emits low-coherent light La, for example, a light source 111 such as SLD (Super Luminescent Diode), ASE (Amplified Spontaneous Emission), or supercontinuum that obtains broadband light by irradiating a nonlinear medium with ultrashort pulse laser light. And an optical system 112 for causing the light emitted from the light source 111 to enter the optical fiber FB1.

  The light splitting means 3 is composed of, for example, a 2 × 2 optical fiber coupler, and splits the light La guided from the light source unit 210 through the optical fiber FB1 into the measurement light L1 and the reference light L2. The light splitting means 3 is optically connected to the two optical fibers FB2 and FB3, respectively. The measurement light L1 is guided through the optical fiber FB2, and the reference light L2 is guided through the optical fiber FB3. The light splitting means 3 in this example also functions as the multiplexing means 4.

  1 is optically connected to the optical fiber FB2, and the measurement light L1 is guided from the optical fiber FB2 to the optical probe 10. The optical probe 10 is inserted into a body cavity from a forceps opening through a forceps channel, for example, and is detachably attached to the optical fiber FB2 by an optical connector 31.

  On the other hand, optical path length adjusting means 220 is arranged on the side of the optical fiber FB3 from which the reference light L2 is emitted. The optical path length adjusting unit 220 changes the optical path length of the reference light L2 in order to adjust the position where the tomographic image acquisition is started, and reflects the reference light L2 emitted from the optical fiber FB3. 22, a first optical lens 21 a disposed between the reflection mirror 22 and the optical fiber FB 3, and a second optical lens 21 b disposed between the first optical lens 21 a and the reflection mirror 22. Yes.

  The first optical lens 21a has a function of converting the reference light L2 emitted from the core of the optical fiber FB3 into parallel light and condensing the reference light L2 reflected by the reflection mirror 22 onto the core of the optical fiber FB3. ing. The second optical lens 21b condenses the reference light L2 converted into parallel light by the first optical lens 21a on the reflection mirror 22, and also converts the reference light L2 reflected by the reflection mirror 22 into parallel light. have. That is, a confocal optical system is formed by the first optical lens 21a and the second optical lens 21b.

  Accordingly, the reference light L2 emitted from the optical fiber FB3 is converted into parallel light by the first optical lens 21a and is condensed on the reflection mirror 22 by the second optical lens 21b. Thereafter, the reference light L2 reflected by the reflection mirror 22 becomes parallel light by the second optical lens 21b, and is condensed on the core of the optical fiber FB3 by the first optical lens 21a.

  The optical path length adjusting means 220 further includes a base 23 on which the second optical lens 21b and the reflecting mirror 22 are fixed, and a mirror moving means 24 for moving the base 23 in the optical axis direction of the first optical lens 21a. is doing. When the base 23 moves in the direction of arrow A, the optical path length of the reference light L2 can be changed.

  Further, the multiplexing means 4 is composed of a 2 × 2 optical fiber coupler as described above, and the reference light L2 whose frequency shift and optical path length have been changed by the optical path length adjusting means 220 and the reflected light L3 from the measurement target Sb. Are combined and emitted to the interference light detection means 240 side via the optical fiber FB4.

  On the other hand, the interference light detecting means 240 detects the interference light L4 between the reflected light L3 combined by the combining means 4 and the reference light L2, and the interference light L4 emitted from the optical fiber FB4 is converted into parallel light. The collimator lens 141 to be converted, the spectroscopic means 142 for separating the interference light L4 having a plurality of wavelength bands for each wavelength band, and the light detection means 144 for detecting the interference light L4 of each wavelength band split by the spectroscopic means 142. And have.

  The spectroscopic means 144 is composed of, for example, a diffraction grating element, etc., and splits the interference light L4 incident thereon and emits the light toward the light detection means 144. The light detection means 144 is composed of, for example, an element such as a CCD in which light sensors are arranged one-dimensionally or two-dimensionally, and each light sensor separates the interference light L4 that has been dispersed as described above for each wavelength band. It comes to detect.

  The light detection means 144 is connected to an image acquisition means 250 made up of a computer system such as a personal computer, for example, and the image acquisition means 250 is connected to a display device 260 made up of a CRT, a liquid crystal display device or the like.

  The operation of the optical tomographic imaging apparatus 1 having the above configuration will be described below. When acquiring a tomographic image, the optical path length is adjusted so that the measurement target Sb is positioned within the measurable region by first moving the base 23 in the direction of arrow A. Thereafter, light La is emitted from the light source unit 210, and this light La is split by the light splitting means 3 into the measurement light L1 and the reference light L2. The measurement light L1 is emitted from the optical probe 10 into the body cavity and irradiated to the measurement object Sb. At this time, the measurement light L1 emitted from the optical probe 10 operating as described above scans the measurement target Sb in a one-dimensional manner. Then, the reflected light L3 from the measuring object Sb is combined with the reference light L2 reflected by the reflecting mirror 22, and the interference light L4 between the reflected light L3 and the reference light L2 is detected by the interference light detection means 240. The detected interference light L4 is subjected to appropriate waveform compensation and noise removal in the image acquisition means 250 and then subjected to Fourier transform, thereby obtaining reflected light intensity distribution information in the depth direction of the measurement target Sb.

  When the measurement light L1 is scanned on the measurement target Sb by the optical probe 10 as described above, information in the depth direction of the measurement target Sb is obtained at each portion along the scanning direction. A tomographic image of a tomographic plane including The tomographic image acquired in this way is displayed on the display device 260. For example, by moving the optical probe 10 in the left-right direction in FIG. 11 and causing the measurement light L1 to scan the measurement target Sb in a second direction orthogonal to the scanning direction, It is also possible to obtain a tomographic image of a tomographic plane including the direction.

  Next, another example of the optical tomographic imaging apparatus to which the optical probe according to the present invention is applied will be described. An optical tomographic imaging apparatus 300 shown in FIG. 12 acquires a tomographic image to be measured by the above-described SS-OCT measurement. Specifically, the optical tomographic imaging apparatus 300 differs from the optical tomographic imaging apparatus 1 of FIG. It is the structure of a unit and an interference light detection means.

  The light source unit 310 in this apparatus emits laser light La while sweeping the frequency at a constant period. Specifically, the light source unit 310 includes a semiconductor optical amplifier (semiconductor gain medium) 311 and an optical fiber FB10, and the optical fiber FB10 is connected to both ends of the semiconductor optical amplifier 311. The semiconductor optical amplifier 311 has a function of emitting weak emission light to one end side of the optical fiber FB10 and amplifying light incident from the other end side of the optical fiber FB10 by injection of driving current. When a driving current is supplied to the semiconductor optical amplifier 311, pulsed laser light La is emitted to the optical fiber FB 1 by an optical resonator formed by the semiconductor optical amplifier 311 and the optical fiber FB 10. .

  Further, an optical branching unit 312 is coupled to the optical fiber FB10, and a part of the light guided in the optical fiber FB10 is emitted from the optical branching unit 312 to the optical fiber FB11 side. Light emitted from the optical fiber FB11 is reflected by a rotating polygon mirror (polygon mirror) 316 via a collimator lens 313, a diffraction grating element 314, and an optical system 315. The reflected light enters the optical fiber FB11 again via the optical system 315, the diffraction grating element 314, and the collimator lens 313.

  Here, the rotary polygon mirror 316 is rotated in the direction of the arrow R1, and the angle of each reflecting surface changes with respect to the optical axis of the optical system 315. As a result, only the light in a specific frequency region out of the light dispersed by the diffraction grating element 314 returns to the optical fiber FB11 again. The frequency of light returning to the optical fiber FB11 is determined by the angle between the optical axis of the optical system 315 and the reflecting surface. Then, light in a specific frequency range that has entered the optical fiber FB11 is incident on the optical fiber FB10 from the optical splitter 312. As a result, laser light La in a specific frequency range is emitted to the optical fiber FB1 side. .

  Therefore, when the rotary polygon mirror 316 rotates at a constant speed in the direction of the arrow R1, the wavelength λ of light incident on the optical fiber FB11 again changes with a constant period as time passes. Thus, the wavelength-swept laser beam La is emitted from the light source unit 310 to the optical fiber FB1 side.

  The interference light detection unit 240 detects the interference light L4 between the reflected light L3 combined by the combining unit 4 and the reference light L2. Then, the image acquisition unit 250 detects the intensity of the reflected light L3 at each depth position of the measurement target Sb by Fourier transforming the interference light L4 detected by the interference light detection unit 240, and the tomogram of the measurement target Sb. Get an image. The acquired tomographic image is displayed on the display device 260. In the apparatus of this example, a detector 40a for detecting the light intensity of the laser light La branched from the optical fiber coupler 2 of the optical fiber FB1 and a detector 40b for detecting the light intensity of the interference light L4 are provided, and interference is performed. The light detection means 240 has a function of adjusting the balance of the light intensity of the interference light L4 based on the output from the detector 40a.

  Here, the detection of the interference light L4 and the generation of the image in the interference light detection means 240 and the image acquisition means 250 will be briefly described. Details of this point are described in “Mitsuo Takeda,“ Optical Frequency Scanning Spectrum Interference Microscope ”, Optical Technology Contact, 2003, Vol41, No7, p426-p432”.

When the measurement light L1 is irradiated onto the measurement object Sb, interference fringes with respect to each optical path length difference l when the reflected light L3 and the reference light L2 from each depth of the measurement object Sb interfere with each other with various optical path length differences. S (l) is the light intensity I (k) detected by the interference light detection means 240,
I (k) = ∫ ₀ ^∞ S (l) [1 + cos (kl)] dl
It is represented by Here, k is the wave number, and l is the optical path length difference. It can be considered that the above equation is given as an interferogram in the optical frequency domain with the wave number k = ω / c as a variable. For this reason, in the image acquisition means 250, the spectral interference fringes detected by the interference light detection means 240 are subjected to Fourier transform, and the light intensity S (l) of the interference light L4 is determined. Distance information and reflection intensity information can be acquired, and a tomographic image can be generated.

  Also in this optical tomographic imaging apparatus 300, the optical probe 10 having the same configuration as that used in the apparatus of FIG. 11 is used, and the operation thereof is the same as in the apparatus of FIG.

  Next, still another example of the optical tomographic imaging apparatus to which the optical probe according to the present invention is applied will be described. An optical tomographic imaging apparatus 400 shown in FIG. 13 acquires a tomographic image to be measured by the TD-OCT measurement described above, and includes a light source unit 210 including a light source 111 and a condenser lens 112 that emit laser light La. And a light splitting means 2 for splitting the laser light La emitted from the light source unit 210 and propagating through the optical fiber FB1, and a light splitting means 3 for splitting the laser light La passing therethrough into the measurement light L1 and the reference light L2. The optical path length adjusting means 220 for adjusting the optical path length of the reference light L2 split by the light splitting means 3 and propagated through the optical fiber FB3, and the measurement light L1 split by the light splitting means 3 and propagated through the optical fiber FB2 An optical probe 10 that irradiates the measuring object S, and a combining means 4 (light) that combines the reflected light L3 and the reference light L2 from the measuring object when the measuring object S1 is irradiated from the optical probe 10 to the measuring object S. Split And the interference light detecting means 240 for detecting the interference light L4 of the reflected light L3 and the reference light L2 combined by the multiplexing means 4.

  The optical path length adjusting means 220 is a mirror that is movable in the direction of arrow A in the figure so as to change the distance between the collimator lens 21 that collimates the reference light L2 emitted from the optical fiber FB3 and the collimator lens 21. 23 and mirror moving means 24 for moving the mirror 23, and has a function of changing the optical path length of the reference light L2 in order to change the measurement position in the measurement object Sb in the depth direction. . Furthermore, a phase modulator 250 is disposed in the optical path of the reference light L2 (optical fiber FB3), and has a function of giving a slight frequency shift to the reference light L2. Then, the reference light L <b> 2 whose optical path length has been changed and frequency shifted by the optical path length adjusting means 220 is guided to the multiplexing means 4.

  The interference light detection means 240 detects the light intensity of the interference light L4 propagated from the multiplexing means 4 through the optical fiber FB2, for example, by heterodyne detection. Specifically, when the sum of the total optical path length of the measurement light L1 and the total optical path length of the reflected light L3 is equal to the total optical path length of the reference light L2, it is strong and weak at the difference frequency between the reference light L2 and the reflected light L3. A beat signal that repeats is generated. As the optical path length is changed by the optical path length adjusting means 220, the measurement position (depth) of the measuring object S changes, and the interference light detection means 240 detects a plurality of beat signals at each measurement position. ing. The information on the measurement position is output from the optical path length adjustment unit 220 to the image acquisition unit.

  Then, based on the beat signal detected by the interference light detection means 240 and the information on the measurement position in the mirror moving means 24, an optical tomographic image is generated by the image acquisition means 250. The generated optical tomographic image is displayed on the display device 260.

  Also in this optical tomographic imaging apparatus 400, an optical probe 10 having the same configuration as that used in the apparatus of FIG. 11 is used, and its operation is the same as that in the apparatus of FIG.

  The optical tomographic imaging apparatus 1, 300, 400 using the optical probe 10 has been described above. Instead of the optical probe 10, the optical probe 100, 110, according to another embodiment of the present invention described above is used. Of course, 120, 130, or 140 can be used.

10, 100, 110, 120, 130, 140 Optical probe
11 Probe outer tube
12 Support member
13 Optical fiber
14 Motor
15 Fiber fixing member
16, 30 bearings
17 Prism mirror
18 Rod lens
31 Coating material L light

Claims (4)

A cylindrical probe outer tube,
A support member disposed in the inner space of the probe outer cylinder so as to extend in the axial direction of the outer cylinder, and capable of rotating around a rotation axis extending in the axial direction;
A plurality of optical fibers that extend alongside the support member in the internal space of the probe outer cylinder and are disposed in a state in which the central axis is deviated from the rotation center of the support member, and are supported by the support member ; ,
Drive means connected to the base end side of the support member and rotating the support member in the circumferential direction of the outer cylinder;
A plurality of optical fibers that are supported by the support member, rotate together with the support member, and are provided for each optical fiber so as to deflect the light emitted from the tip of the optical fiber in the circumferential direction of the outer cylinder. An optical deflection element;
Condensing means for condensing the light emitted from the tip of the optical fiber and converging it in a scanned object disposed on the outer periphery of the probe outer cylinder;
An optical probe comprising light guide means for guiding light reflected by the scanned object to the tip of the optical fiber and causing the light to enter the optical fiber from the tip.   2. The optical probe according to claim 1, wherein one of the optical fibers and one of the optical deflecting elements provided for the optical fiber are dedicated to light transmission or light reception.   2. The optical probe according to claim 1, wherein one of the optical fibers and one optical deflection element provided for the optical fiber are used for both light transmission and light reception. A light source that emits light;
A light splitting means for splitting light emitted from the light source into measurement light and reference light;
An irradiation optical system for irradiating the measurement object with the measurement light;
A multiplexing means for multiplexing the reflected light from the measurement object and the reference light when the measurement object is irradiated with the measurement light;
Interference light detection means for detecting interference light between the reflected light and the reference light combined;
Based on the detected frequency and intensity of the interference light, the intensity of the reflected light at a plurality of depth positions of the measurement object is detected, and the tomography of the measurement object is detected based on the intensity of the reflected light at each depth position. In an optical tomographic imaging apparatus comprising an image acquisition means for acquiring an image,
An optical tomographic imaging apparatus, wherein the irradiation optical system includes the optical probe according to any one of claims 1 to 3.

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