JP2010167029A - Optical tomographic image acquisition apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an optical tomographic image with suitable image quality according to a user's purpose which is capable of changing a rotation speed of a probe. <P>SOLUTION: In an optical tomographic image acquisition apparatus, an optical probe rotates for scanning to obtain a reflected signal from a measured subject, and an optical tomographic image of the measured subject is formed based on the obtained reflected signal, and the optical tomographic image acquisition apparatus is provided and characteristically including rotation speed changing means which changes the rotation speed of the optical probe in a plurality of stages. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to an optical tomographic image acquisition apparatus, and more particularly to an optical tomographic image acquisition apparatus that acquires an optical tomographic image of a biological tissue by inserting an optical probe into a body cavity in order to observe and diagnose the biological tissue.

  Conventionally, an optical tomographic imaging apparatus (optical tomographic image acquisition apparatus) using an optical coherence tomography (OCT) measurement method is known as a method for acquiring a cross-sectional image without cutting a measurement target such as a biological tissue. ing.

  This OCT measurement method is a kind of optical interferometry, in which light emitted from a light source is divided into measurement light and reference light, and the optical path length of the measurement light and reference light is within the coherence length of the light source. This is a measurement method using the fact that optical interference is detected only when the ranges match.

  Using such an optical tomographic image acquisition apparatus (OCT apparatus), an optical probe (OCT probe) is inserted into the forceps opening of the endoscope apparatus to guide the signal light and the reflected light of the signal light, and the light in the body cavity By acquiring a tomographic image, it is possible to observe and diagnose a living tissue.

For example, by rotating the optical fiber in the optical scanning probe at a constant speed and radiating in a direction perpendicular to the axis of the optical scanning probe while irradiating low interference light, tomographic image data inside the living tissue is obtained. An optical tomographic image apparatus that acquires a two-dimensional tomographic image is known (see, for example, Patent Document 1).
JP 2000-131222 A

  However, in the above-mentioned conventional one, only one rotation speed is assumed to be set as the rotation speed of the optical probe. For this reason, there is a problem that the resolution is too coarse depending on the use of the user, or conversely, the resolution is too fine and too time consuming.

  The present invention has been made in view of such circumstances, and an optical tomographic image that can switch the rotation speed of an optical probe and can provide an optical tomographic image with suitable image quality according to a user's application. An object is to provide an acquisition device.

  In order to achieve the above-mentioned object, the invention according to claim 1 rotationally scans the optical probe, acquires a reflection signal from the measurement object, and forms an optical tomographic image of the measurement object based on the acquired reflection signal. An optical tomographic image acquisition apparatus, comprising: a rotational speed switching means for switching the rotational speed of the optical probe in a plurality of stages.

  As a result, the rotation speed of the optical probe can be switched, and an optical tomographic image with suitable image quality can be acquired according to the user's application.

  According to a second aspect of the present invention, the optical probe is inserted into a body cavity from a forceps port of an endoscope.

  Accordingly, the user can acquire an optical tomographic image having a suitable image quality according to the user's application while viewing a normal endoscopic image and OCT image.

  According to a third aspect of the present invention, the rotation speed switching means is a remote controller.

  According to a fourth aspect of the present invention, the rotation speed switching means is a controller attached to an operation unit of an endoscope.

  Thereby, it becomes possible for the user to appropriately switch the rotation speed of the optical probe by his / her own intention using the controller.

  The optical tomographic image acquisition apparatus according to claim 1 or 2, further comprising display means for displaying the optical tomographic image, wherein the optical tomographic image is displayed on the display means. The rotational speed of the optical probe when the optical tomographic image is instructed to be stored is slower than the rotational speed of the optical probe when displaying in real time.

  Further, as shown in claim 6, the optical tomographic image acquisition apparatus according to claim 1 or 2, further comprising a linear moving speed detecting means for detecting a moving speed in a longitudinal direction of the optical probe, The movement speed in the longitudinal direction of the probe detected by the linear movement speed detection means is higher than the rotation speed of the optical probe when the movement speed in the longitudinal direction of the probe detected by the linear movement speed detection means is larger than a certain value. The rotational speed of the optical probe when it is less than or equal to the predetermined value is slowed down.

  According to a seventh aspect of the present invention, the linear moving speed detecting means is an acceleration sensor attached to the optical probe for detecting an acceleration in which the optical probe moves in the longitudinal direction. .

  In addition, as shown in claim 8, the optical tomographic image acquisition apparatus according to claim 2, further comprising display means for displaying the optical tomographic image, wherein the inner part displayed on the display means. Linear movement speed detection means for detecting the movement speed in the longitudinal direction of the optical probe by image processing on a normal endoscopic image including an image of the tip of the optical probe imaged by an endoscope, and the linear movement speed The movement speed in the longitudinal direction of the probe detected by the linear movement speed detection means is higher than the rotation speed of the optical probe when the movement speed in the longitudinal direction of the probe detected by the detection means is larger than a certain value. The rotational speed of the optical probe is slowed in the following cases.

  This allows the system to determine the state of observation of the measurement target by the user and automatically switch the rotation speed of the optical probe, allowing the user to make a diagnosis without being aware of the rotation speed of the optical probe. I can concentrate on it.

  As described above, according to the present invention, the rotation speed of the optical probe can be switched, and an optical tomographic image with suitable image quality can be acquired according to the user's application.

  Hereinafter, an optical tomographic image acquisition apparatus according to the present invention will be described in detail with reference to the accompanying drawings.

  FIG. 1 is a block diagram showing a schematic configuration of an optical tomographic image acquisition apparatus according to the first embodiment of the present invention.

  An optical tomographic image acquisition apparatus 10 of the present embodiment shown in FIG. 1 acquires an optical tomographic image of a measurement object by an optical coherence tomography (OCT) measurement method, particularly TD-OCT (Time Domain OCT). is there. The optical tomographic image acquisition apparatus 10 of the present embodiment branches a light source unit (light source unit) 12 that emits light La for measurement, and the light La emitted from the light source unit 12 into measurement light L1 and reference light L2. At the same time, the return light L3 and the reference light L2 from the measurement target S, which is the subject, are combined and an optical fiber coupler (branching / combining unit) 14 that generates interference light L4 and L5 and the optical fiber coupler 14 are branched. The optical probe (optical probe device) 16 including the rotation-side optical fiber FB1 that guides the measured light L1 to the measurement target and guides the return light L3 from the measurement target, and the measurement light L1 to the rotation-side optical fiber FB1. The fixed-side optical fiber FB2 that guides the return light L3 guided along with the rotation-side optical fiber FB1, and the rotation-side optical fiber FB1 can rotate with respect to the fixed-side optical fiber FB2. The optical rotary adapter 18 that transmits the measurement light L1 and the return light L3, the interference light detection unit 20 that detects the interference lights L4 and L5 generated by the optical fiber coupler 14 as interference signals, and this interference light detection The processing unit 22 that processes the interference signal detected by the unit 20 to acquire an optical tomographic image (hereinafter also simply referred to as “tomographic image” or “OCT image”) and the tomographic image acquired by the processing unit 22 are displayed. Display unit 24.

  In addition, the optical tomographic image acquisition apparatus 10 is combined with the optical path length adjustment unit 26 that adjusts the optical path length of the reference light L2, the optical fiber coupler 28 that splits the light La emitted from the light source unit 12, and the optical fiber coupler 14. Detectors 30a and 30b that detect the waved interference lights L4 and L5, respectively, and a control operation unit 32 that inputs various conditions to the processing unit 22 and the display unit 24, changes settings, and the like.

  As will be described later, in the optical tomographic image acquisition apparatus 10 shown in FIG. 1, various light including the above-described emission light La, measurement light L1, reference light L2, return light L3, and the like is transmitted between components such as optical devices. Various optical fibers FB (FB3, FB4, FB5, FB6, FB7, etc.) including the rotation-side optical fiber FB1 and the fixed-side optical fiber FB2 are used as light paths for guiding and transmitting in FIG.

  The light source unit 12 emits OCT signal light (for example, laser light having a wavelength of 1.3 μm). For example, the light source unit 12 emits low-coherence light La such as SLD (Super Luminescent Diode) or ASE (Amplified Spontaneous Emmision). The light source 12a which injects | emits and the lens (optical system) 12b for condensing the low coherent light La inject | emitted from the light source 12a and injecting into optical fiber FB4 are provided. The light La emitted from the light source unit 12 is input to the optical fiber coupler 14 through the optical fibers FB4 and FB3.

  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 optical fiber FB2, the optical fiber FB3, the optical fiber FB5, and the optical fiber FB7. .

  The optical fiber coupler 14 splits the light La incident from the light source unit 12 through the optical fiber FB4, the optical fiber couplers 28, and FB3 into the measurement light L1 and the reference light L2. The measurement light L1 is input to the optical rotary adapter 18 via the optical fiber FB2, and the reference light L2 is input to the optical path length adjustment unit 26 via the optical fiber FB5.

  Furthermore, the optical fiber coupler 14 is reflected by the measurement target S and the reference light L2 that has been subjected to frequency shift and change of the optical path length by the optical path length adjustment unit 26 and returned to the optical fiber FB5, as will be described later. The acquired return light L3 guided from the optical fiber FB1 and the optical fiber FB2 is multiplexed and emitted to the optical fiber FB3 and the optical fiber FB6.

  The optical probe 16 is connected to the optical fiber FB2 via the optical rotary adapter 18. The measurement light L1 is input from the optical fiber FB2 to the optical fiber FB1 in the optical probe 16 through the optical rotary adapter 18. The input measurement light L1 is transmitted through the optical fiber FB1 and irradiated onto the measurement object S. Then, the optical probe 16 acquires the return light L3 reflected by the measuring object S, transmits the acquired return light L3 through the optical fiber FB1, and emits it to the optical fiber FB2 through the optical rotary adapter 18. It has become.

  The optical rotary adapter 18 optically connects the fixed optical fiber FB2 and the optical fiber FB1 rotating in the optical probe 16.

  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 optical tomographic image acquisition apparatus 10 is provided on the optical path of the optical fiber FB6 branched from the optical fiber coupler 28 and detects the light intensity of the interference light L4, and the interference provided on the optical fiber FB7. And a detector 30b for detecting the light intensity of the light L5.

  The interference light detection unit 20 adjusts the balance of the intensity of the interference light L4 detected from the optical fiber FB6 and the intensity of the interference light L5 detected from the optical fiber FB7 based on the detection results of the detectors 30a and 30b.

  The interference light detection unit 20 detects the light intensity of the interference light L4 by, for example, 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 return light L3 is equal to the total optical path length of the reference light L2, it is strong or weak at the difference frequency between the reference light L2 and the return light L3. A beat signal that repeats is generated. As the optical path length is changed by the optical path length adjustment unit 26, the measurement position in the depth direction of the measurement target S changes, and the interference light detection unit 20 detects a plurality of beat signals at each measurement position. ing.

  Information on the measurement position is output from the optical path length adjustment unit 26 to the interference light detection unit 20 and the processing unit 22. An optical tomographic image is generated in the processing unit 22 based on the beat signal detected by the interference light detection unit 20 and information on the measurement position in the mirror drive mechanism 42.

  The processing unit 22 acquires a tomographic image from the interference signal detected by the interference light detection unit 20 in this way. Specifically, the region where the optical probe 16 and the measurement target S are in contact at the measurement position, more precisely, the surface of the probe outer tube (sheath) of the optical probe 16 and the surface of the measurement target S are in contact. A region that can be regarded as being present is detected by a signal from the optical rotary adapter 18, and a tomographic image is acquired from the interference signal detected by the interference light detector 20.

  The display unit 24 includes a CRT or a liquid crystal display device, and displays the tomographic image transmitted from the processing unit 22.

  The optical path length adjustment unit 26 has a function of changing the optical path length of the reference light L2 in order to change the measurement position in the measurement target S in the depth direction, and the reference light L2 emission side (that is, the optical fiber FB5). The optical fiber FB5 is disposed at the end opposite to the optical fiber coupler 14). A phase modulator 34 is disposed in the middle of the optical fiber FB5 that is the optical path of the reference light L2. The phase modulator 34 has a function of giving a slight frequency shift to the reference light L2.

  The optical path length adjustment unit 26 changes the optical path length of the reference light L2, and includes an optical system 36 and a reflection mirror 38. The optical system 36 has a function of converting the reference light L2 emitted from the optical fiber FB5 into parallel light and condensing the reference light L2 reflected from the reflection mirror 38 onto the optical fiber FB5. The reflection mirror 38 is disposed on the movable stage 40, and the movable stage 40 is provided so as to be movable in the arrow A direction by a mirror driving mechanism 42. When the movable stage 40 moves in the direction of the arrow A, the optical path length of the reference light L2 is changed. In this way, the optical path length of the reference light L2 is adjusted.

  The control operation unit 32 includes input means such as a keyboard and a mouse, and control means for managing various conditions based on the input information, and is connected to the processing unit 22 and the display unit 24. The control operation unit 32 inputs, sets, and changes various processing conditions in the processing unit 22 and changes the display setting of the display unit 24 based on an operator instruction input from the input unit.

  Note that the control operation unit 32 may display an operation screen on the display unit 24, or may provide a separate display unit to display the operation screen.

  At the time of measurement, the optical fiber FB1 in the optical probe 16 rotates as indicated by an arrow in the figure, and the measurement light L1 is irradiated while rotating with respect to the measuring object S from the light emitting unit 44 installed at the tip thereof. Is done. In this way, the optical probe 16 rotates (to be precise, the light emitting portion 44 in the optical probe 16 rotates, but this is also simply referred to as the optical probe 16 rotating), thereby providing a two-dimensional fault. An image can be obtained.

  An example of the OCT image (optical tomographic image) of the measuring object S at this time is schematically shown in FIG.

  The processing unit 22 acquires the interference signal (tomographic information) IS for one cycle (for one line) acquired by the interference light detection unit 20 in the radial direction of the optical probe 16 (the direction indicated by the arrow R in the figure). One tomographic image B as shown in FIG. 2 is generated. A black portion indicated by reference numeral 50 in the drawing represents an observation site where the optical probe 16 contacts the measuring object S.

  Further, each point arranged on the circumference in FIG. 2 represents each scan (scan), α is each scan interval of the interferometer, and this is the image resolution (resolution) in the radial direction. Therefore, when the probe rotation speed is low, the radial scan interval becomes narrow and high resolution is obtained. Conversely, when the probe rotation speed is high, the radial scan interval becomes wide and low resolution is obtained.

  At this time, when the user is searching for an observation site, the resolution may be low, so it is preferable that the field of view can be quickly observed by moving to various sites, and when the affected area is found and diagnosed, it is preferable that the observation can be performed with high resolution. . Therefore, the optical tomographic image acquisition apparatus 10 of the present invention can switch the probe rotation speed (the rotation speed of the light emitting unit 44 in the optical probe 16) in accordance with the user's application.

  First, the first embodiment allows the user himself to switch the probe rotation speed.

  Therefore, the optical tomographic image acquisition apparatus 10 of the first embodiment includes a rotation speed storage unit 46 and a user speed change unit 48 as shown in FIG.

  The rotational speed storage unit 46 stores a plurality of preset probe rotational speeds. When the user changes the probe rotation speed initially set in the system, the user sets a predetermined probe rotation speed from the probe rotation speeds stored in the rotation speed storage unit 46 via the user speed change unit 48. specify. Then, the designated probe rotation speed is sent to the control operation section 32, and the control operation section 32 sends a signal to the optical rotary adapter 18 to control the optical probe 16 to rotate at the designated probe rotation speed.

  3 and 4 show examples of the user speed changing unit 48. FIG.

  First, the example shown in FIG. 3 is a remote-type speed change controller independent of the endoscope. The endoscope (endoscope scope) 50 inserts its distal end portion 52 into the body cavity and observes the measurement site. Separately from this, the user speed changing unit 48 operates as a user-operated speed. A change controller 54 is installed.

  In the example shown in FIG. 3, the speed change controller 54 has two buttons, a “slow” button and a “speed” button for switching the rotation speed between two stages of low-speed rotation and high-speed rotation set in the rotation speed storage unit 46 in advance. Has a button. As a result, when searching for an affected area by switching the field of view, the user can press the “fast” button to change the probe rotation speed to a high speed. However, when carefully observing and diagnosing, the “slow” button can be pressed to set the probe rotation speed to a low speed, thereby enabling diagnosis with high resolution.

  The speed change controller 54 may be provided with speed change buttons having more than two stages, and the speed change to more stages may be possible. The connection between the control operation unit 32 and the speed change controller 54 may be wired. Good or wireless.

  In addition, instead of preparing a special controller as described above, a configuration in which the user can instruct a change in the rotation speed from the keyboard of the control operation unit 32 may be employed.

  FIG. 4 shows another example of the user speed changing unit 48. In the example shown in FIG. 4, a speed change controller 56 having a speed switching button for switching the probe rotation speed is provided on the operation unit 53 of the endoscope 50. When the user presses the speed switching button of the speed change controller 56, the probe rotation speed is switched.

  The endoscope 50 is provided with a forceps port 58, and the optical probe 16 (not shown in FIG. 4) is inserted from the forceps port 58 and protrudes from the distal end portion 52.

  As described above, in the present embodiment, the user is provided with means for switching the probe rotation speed so that the user can manually switch the probe rotation speed. Depending on the purpose, the probe rotation speed can be appropriately switched at the user's will.

  Next, a second embodiment of the present invention will be described.

  In the second embodiment, the probe rotation speed is automatically switched in accordance with the image display mode on the display unit 24. When the image is displayed on the display unit 24 in real time, the user is searching for a field of view while viewing the image. On the other hand, when the user is making a diagnosis, the user It is an instruction to save. Therefore, the probe rotation speed is switched in accordance with the state of image display indicating whether image storage is instructed in such real-time display. That is, when the image is displayed in real time, the probe rotation speed is increased, and when the user instructs image storage, the probe rotation speed is switched so as to decrease the probe rotation speed.

  FIG. 5 shows an example of the display screen of the display unit 24 in this case.

  As shown in FIG. 5, on the display screen 60, an endoscopic image and an OCT image (tomographic image) are displayed side by side in real time. The user searches the visual field by moving the optical probe 16 (see FIG. 1) while viewing these endoscope images and OCT images.

  As shown in FIG. 5, an image 62 of the distal end portion of the optical probe 16 is displayed in the endoscopic image. If the user sees this and the OCT image and determines that the optical probe 16 has arrived at the affected area, the user clicks an “image save key” displayed on the display screen 60 to instruct the image save.

  The control operation unit 32 switches the probe rotation speed to a slow speed so that a high-resolution tomographic image can be acquired.

  Thus, in the case of this embodiment, the system automatically determines the probe rotation speed based on the state of the image display whether the user is searching for a visual field or is in a diagnosis state. Since switching is performed, the user can concentrate on observation by operating the optical probe 16 without worrying about the rotation speed.

  Next, a third embodiment of the present invention will be described.

  In the third embodiment, the linear movement in the longitudinal direction (axial direction) of the optical probe operated by the user is detected, and the probe rotation speed is switched according to the linear movement speed of the optical probe. .

  That is, when the optical probe 16 inserted into the body cavity from the forceps port is taken in and out in the longitudinal direction (axial direction) and moved linearly at a speed equal to or higher than a certain speed, the field of view is searched. When this linear moving speed is below a certain level, it is considered that the diagnosis is being performed. Therefore, when the linear moving speed of the optical probe 16 is detected and the linear moving speed of the optical probe 16 is below a certain value, the probe rotating speed is increased. Switch the probe rotation speed to

  FIG. 6 shows a schematic configuration of the optical tomographic image acquisition apparatus according to the third embodiment.

  As shown in FIG. 6, the optical tomographic image acquisition apparatus 100 of the present embodiment has substantially the same configuration as the optical tomographic image acquisition apparatus 10 of the first embodiment shown in FIG. That is, a probe movement detection unit 70 is provided instead of the rotation speed storage unit 46 and the user speed change unit 48 of the optical tomographic image acquisition apparatus 10 of FIG.

  Therefore, constituent elements other than the probe movement detection unit 70 are denoted by the same reference numerals as those of the optical tomographic image acquisition apparatus 10 in FIG.

  The probe movement detection unit 70 detects a linear movement in the longitudinal direction of the optical probe 16 inserted into the body cavity via the forceps opening of the endoscope. The user moves the optical probe 16 inserted into the body cavity in and out of the longitudinal direction and observes the measuring object S. The probe movement detector 70 detects the linear moving speed of the optical probe 16 at that time.

  The detected linear moving speed of the optical probe 16 is sent to the control operation unit 32. In the control operation unit 32, it is determined whether or not the sent linear moving speed is larger than a predetermined constant speed. If it is larger than the predetermined constant speed, the probe rotation speed is switched to a higher speed and the user quickly searches for a visual field. It can be so. Further, when the linear moving speed is below a certain speed, the probe rotation speed is switched to a slow speed so that the user can make a careful diagnosis.

  An example of the probe movement detection unit 70 is shown in FIGS.

  First, a first example of the probe movement detection unit 70 shown in FIG. 7 is an acceleration sensor 72 attached to the optical probe 16.

  The acceleration sensor 72 is fixedly attached to, for example, an outer tube (sheath) of the optical probe 16 and moves together with the optical probe 16 according to the linear movement of the optical probe 16 to detect the linear movement speed. Is. A detection signal of the acceleration sensor 72 is sent to the control operation unit 32. The control operation unit 32 detects the linear movement speed of the optical probe 16 based on the detection signal of the acceleration sensor 72, and thereby controls switching of the probe rotation speed.

  Further, the second example of the probe movement detection unit 70 detects an image of the optical probe 16 from a normal endoscopic image without providing a special component, and performs linear movement by image processing in the control operation unit 32. The speed is detected.

  As shown in FIG. 8, an image 62 of the distal end portion of the optical probe 16 is displayed on the endoscopic image displayed on the display screen of the display unit 24. A change in the position of the optical probe 16 is detected by pattern matching of the shape of the image 62 at the tip of the optical probe 16 that changes with time, and the linear movement speed is detected by the control operation unit 32.

  Alternatively, a linear movement speed of the optical probe 16 may be detected by attaching a mark on the optical probe 16 and tracking the mark.

  In either case, when the detected linear movement speed of the optical probe 16 is faster than a certain value, the probe rotation speed is increased. When the detected linear movement speed of the optical probe 16 is less than a certain value, the probe rotation speed is increased. To slow down.

  As described above, also in the present embodiment, since the linear movement speed of the optical probe 16 is detected and the probe rotation speed is automatically switched, the measurement target S can be obtained without the user being aware of the probe rotation speed. Can concentrate on observation.

  In the embodiment described above, the probe rotation speed is switched between two stages: a high rotation speed when the user searches the visual field to find the affected area, and a low rotation speed when the affected area is found and diagnosed. However, switching of the probe rotation speed is not limited to such two-stage switching, and may be switched to a larger number of stages of rotation speed. For example, different probe rotation speeds may be set and switched according to differences in the site of the measurement target S such as the stomach, intestine, and trachea.

  In the example described above, the optical probe 16 is inserted into the body cavity through the forceps opening of the endoscope. However, when the optical probe 16 is used by being inserted into the body cavity through the forceps opening as described above. For example, the present invention is applicable to fundus examinations.

  The optical tomographic image acquisition apparatus of the present invention has been described in detail above, but the present invention is not limited to the above examples, and various improvements and modifications may be made without departing from the scope of the present invention. Of course.

1 is a block diagram illustrating a schematic configuration of an optical tomographic image acquisition apparatus according to a first embodiment of the present invention. It is explanatory drawing which shows an example of the OCT image of the measuring object S typically. It is explanatory drawing which shows an example of a user speed change part. It is explanatory drawing which shows the other example of a user speed change part. It is explanatory drawing which shows the example of the display screen of the display apparatus for demonstrating 2nd Embodiment of this invention. It is a block diagram which shows schematic structure of the optical tomographic image acquisition apparatus which concerns on 3rd Embodiment of this invention. It is explanatory drawing which shows an example of a probe movement detection part. It is explanatory drawing for demonstrating the other example of a probe movement detection part.

  DESCRIPTION OF SYMBOLS 10 ... Optical tomographic image acquisition apparatus (1st Embodiment), 12 ... Light source part, 14 ... Optical fiber coupler, 16 ... Optical probe, 18 ... Optical rotary adapter, 20 ... Interference light detection part, 22 ... Processing part, 24 DESCRIPTION OF SYMBOLS ... Display part 26 ... Optical path length adjustment part 32 ... Control operation part 46 ... Rotation speed memory | storage part 48 ... User speed change part 54 ... Speed change controller 56 ... Speed switch button 70 ... Probe movement detection part, 72. Acceleration sensor

Claims (8)

An optical tomographic image acquisition apparatus that rotationally scans an optical probe, acquires a reflection signal from a measurement target, and forms an optical tomographic image of the measurement target based on the acquired reflection signal,
An optical tomographic image acquisition apparatus comprising a rotation speed switching means for switching the rotation speed of the optical probe in a plurality of stages.   The optical tomographic image acquisition apparatus according to claim 1, wherein the optical probe is inserted into a body cavity from a forceps opening of an endoscope.   The optical tomographic image acquisition apparatus according to claim 1, wherein the rotation speed switching unit is a remote controller.   The optical tomographic image acquisition apparatus according to claim 1, wherein the rotation speed switching unit is a controller mounted on an operation unit of an endoscope.   3. The optical tomographic image acquisition apparatus according to claim 1, further comprising display means for displaying the optical tomographic image, wherein the optical probe rotates when the optical tomographic image is displayed in real time on the display means. An optical tomographic image acquisition apparatus characterized in that the rotational speed of the optical probe when instructing the storage of the optical tomographic image is slower than the speed.   The optical tomographic image acquisition apparatus according to claim 1, further comprising a linear moving speed detecting unit that detects a moving speed in a longitudinal direction of the optical probe, and the probe detected by the linear moving speed detecting unit. The optical probe when the moving speed in the longitudinal direction of the probe detected by the linear moving speed detecting means is less than or equal to the fixed value than the rotational speed of the optical probe when the moving speed in the longitudinal direction is greater than a certain value An optical tomographic image acquisition apparatus characterized by slowing the rotational speed of the optical tomographic image.   The optical tomographic image acquisition according to claim 6, wherein the linear moving speed detecting means is an acceleration sensor attached to the optical probe for detecting an acceleration in which the optical probe moves in a longitudinal direction. apparatus.   The optical tomographic image acquisition apparatus according to claim 2, further comprising display means for displaying the optical tomographic image, and the optical probe displayed on the display means and imaged by the endoscope. It comprises linear movement speed detection means for detecting the movement speed in the longitudinal direction of the optical probe by image processing on a normal endoscopic image including an image of the tip, and the longitudinal direction of the probe detected by the linear movement speed detection means The rotation speed of the optical probe when the movement speed in the longitudinal direction of the probe detected by the linear movement speed detection means is less than or equal to the predetermined value, rather than the rotation speed of the optical probe when the movement speed of the optical probe is greater than a certain value An optical tomographic image acquisition apparatus characterized by slowing the direction.

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