WO2015102081A1 - 光イメージング用プローブ - Google Patents
光イメージング用プローブ Download PDFInfo
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- WO2015102081A1 WO2015102081A1 PCT/JP2014/084003 JP2014084003W WO2015102081A1 WO 2015102081 A1 WO2015102081 A1 WO 2015102081A1 JP 2014084003 W JP2014084003 W JP 2014084003W WO 2015102081 A1 WO2015102081 A1 WO 2015102081A1
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- optical path
- optical
- rotation
- motor
- path conversion
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- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B6/00—Light guides; Structural details of arrangements comprising light guides and other optical elements, e.g. couplings
- G02B6/24—Coupling light guides
- G02B6/36—Mechanical coupling means
- G02B6/3616—Holders, macro size fixtures for mechanically holding or positioning fibres, e.g. on an optical bench
- G02B6/3624—Fibre head, e.g. fibre probe termination
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- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B23/00—Telescopes, e.g. binoculars; Periscopes; Instruments for viewing the inside of hollow bodies; Viewfinders; Optical aiming or sighting devices
- G02B23/24—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes
- G02B23/26—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes using light guides
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0062—Arrangements for scanning
- A61B5/0066—Optical coherence imaging
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
- A61B5/0084—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for introduction into the body, e.g. by catheters
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- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B26/00—Optical devices or arrangements for the control of light using movable or deformable optical elements
- G02B26/08—Optical devices or arrangements for the control of light using movable or deformable optical elements for controlling the direction of light
- G02B26/0875—Optical devices or arrangements for the control of light using movable or deformable optical elements for controlling the direction of light by means of one or more refracting elements
- G02B26/0883—Optical devices or arrangements for the control of light using movable or deformable optical elements for controlling the direction of light by means of one or more refracting elements the refracting element being a prism
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- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B26/00—Optical devices or arrangements for the control of light using movable or deformable optical elements
- G02B26/08—Optical devices or arrangements for the control of light using movable or deformable optical elements for controlling the direction of light
- G02B26/10—Scanning systems
- G02B26/108—Scanning systems having one or more prisms as scanning elements
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- G—PHYSICS
- G02—OPTICS
- G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
- G02B6/00—Light guides; Structural details of arrangements comprising light guides and other optical elements, e.g. couplings
- G02B6/24—Coupling light guides
- G02B6/36—Mechanical coupling means
- G02B6/3604—Rotary joints allowing relative rotational movement between opposing fibre or fibre bundle ends
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- G—PHYSICS
- G03—PHOTOGRAPHY; CINEMATOGRAPHY; ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ELECTROGRAPHY; HOLOGRAPHY
- G03B—APPARATUS OR ARRANGEMENTS FOR TAKING PHOTOGRAPHS OR FOR PROJECTING OR VIEWING THEM; APPARATUS OR ARRANGEMENTS EMPLOYING ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ACCESSORIES THEREFOR
- G03B15/00—Special procedures for taking photographs; Apparatus therefor
- G03B15/02—Illuminating scene
- G03B15/03—Combinations of cameras with lighting apparatus; Flash units
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- G—PHYSICS
- G03—PHOTOGRAPHY; CINEMATOGRAPHY; ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ELECTROGRAPHY; HOLOGRAPHY
- G03B—APPARATUS OR ARRANGEMENTS FOR TAKING PHOTOGRAPHS OR FOR PROJECTING OR VIEWING THEM; APPARATUS OR ARRANGEMENTS EMPLOYING ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ACCESSORIES THEREFOR
- G03B35/00—Stereoscopic photography
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- G—PHYSICS
- G03—PHOTOGRAPHY; CINEMATOGRAPHY; ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ELECTROGRAPHY; HOLOGRAPHY
- G03B—APPARATUS OR ARRANGEMENTS FOR TAKING PHOTOGRAPHS OR FOR PROJECTING OR VIEWING THEM; APPARATUS OR ARRANGEMENTS EMPLOYING ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ACCESSORIES THEREFOR
- G03B37/00—Panoramic or wide-screen photography; Photographing extended surfaces, e.g. for surveying; Photographing internal surfaces, e.g. of pipe
- G03B37/005—Photographing internal surfaces, e.g. of pipe
Definitions
- the present invention relates to a three-dimensional scanning type optical imaging probe for three-dimensionally capturing and observing light reflected by a subject in an apparatus machine or the like.
- Diagnostic imaging technology is a technology that is widely used in fields such as machine equipment and medical treatment.
- a tomographic image or a three-dimensional tomographic image in addition to a general camera observation or an ultrasonic diagnostic apparatus.
- Possible methods such as X-ray CT, nuclear magnetic resonance, and OCT images (optical coherence tomography) using light coherence have been studied and utilized.
- OCT diagnostic imaging technique capable of obtaining the finest captured image among these methods has attracted particular attention.
- OCT images often use near-infrared light having a wavelength of about 1300 nm (nanometers) or laser light having a wavelength of about 400 nm as a light source.
- an excellent spatial resolution of about 10 ⁇ m (micron) or less [1/10 or less of an ultrasonic diagnostic apparatus] can be achieved.
- Near-infrared light as a light source is non-invasive to living organisms, and is expected to be used for finding, diagnosing and treating affected areas in blood vessels such as the stomach, small intestine, and arterial flow in the medical field. Yes.
- a typical structure of an OCT endoscope to which these device machine and medical OCT imaging technologies are applied is as shown in Patent Document 1, for example.
- the present invention has been made in view of the above-described conventional circumstances, and the problem is to reduce the occurrence of rotation transmission delay, torque loss, etc., thereby reducing rotational unevenness and shaft runout of a rotating mechanism that radiates light.
- a probe for three-dimensional scanning optical imaging that can prevent rubbing and rotation transmission delay and can obtain a fixed range of three-dimensional scanning and stereoscopic observation images not only in the rotation direction but also in the forward direction, and solve these problems simultaneously. Is to provide.
- One means for solving the above-mentioned problems is a probe for optical imaging that guides light incident on the distal end side to the rear side, a fixed-side optical fiber that is non-rotatably built in a substantially tubular catheter, and the fixed side
- a first optical path conversion unit that is positioned on the distal end side of the optical fiber, is driven to rotate by a first motor, and radiates the light beam forward at an angle with respect to the rotation center, the fixed-side optical fiber, and the first optical path
- a rotation-side optical fiber that is optically connected by a rotary optical connector and is driven to rotate by a second motor, and an optical path that is tilted by a small angle with respect to the rotation center at the tip side of the rotation-side optical fiber.
- the second optical path changing means for rotating and radiating the light toward the first optical path means is arranged substantially on the same line, and the first optical path changing means and the second optical path changing hand are arranged. Changing the radiation angle of the light beam by controlling the rotation speed of the two motors, by emitting a light beam to the three-dimensional region of the front, is intended to obtain a high-quality three-dimensional observation image.
- the optical fiber is not rubbed in a catheter such as an endoscope apparatus, and the occurrence of rotation transmission delay, torque loss, and the like is reduced. Furthermore, each of the first optical path changing means and the second optical path changing means can independently rotate so that a light beam can be emitted to the front three-dimensional region, and space in an OCT endoscope using near infrared light, laser light, or the like. A three-dimensional observation image with high resolution can be obtained.
- the first feature of the optical imaging probe according to the present embodiment is that the optical fiber probe that guides the light incident on the distal end side to the rear side is arranged in a non-rotatable manner and is incorporated in a substantially tubular catheter.
- a first optical path conversion means that is positioned on the distal end side of the fixed-side optical fiber, is driven to rotate by a first motor, and rotates and radiates light rays at an angle with respect to the rotation center; and the fixed-side optical fiber;
- a rotation-side optical fiber positioned between the first optical path changing means, optically connected by a rotary optical connector, and driven to rotate by a second motor;
- Second optical path conversion means for rotating and radiating the optical path at a slight angle and irradiating the first optical path means with the light path is disposed on substantially the same line, and the light is transmitted to the fixed side optical fiber.
- each of the first optical path changing means and the second optical path changing means can independently rotate so that a light beam can be emitted to the front three-dimensional region, and space in an OCT endoscope using near infrared light, laser light, etc. A three-dimensional observation image with high resolution can be obtained.
- the rotating shaft of the first motor has a hollow shape
- the first optical path changing means is fixed to the rotating shaft and rotates
- the rotating side optical fiber passes through the hollow hole rotatably
- the rotation shaft of the second motor is also hollow, and the rotation side optical fiber is fixed and rotated in this hole.
- the first optical path conversion means is constituted by a rotatable prism. According to this configuration, the light beam passes through the first optical path changing means, and a wide range of forward three-dimensional scanning is possible.
- the second optical path changing means is constituted by a prism having a substantially flat surface inclined at the tip.
- the first pulse generating means for generating at least one pulse per rotation according to the rotation angle of the first motor, and at least one rotation according to the rotation angle of the second motor.
- a second pulse generating means for generating one or more pulses, a control means for adjusting the rotational speeds of the first and second motors by the pulses from the first and second pulse generating means;
- the condenser lens, the first prism, and the second prism are arranged on a substantially straight line.
- the second optical path changing unit can emit light in a wide angular range.
- the first optical path conversion means is configured such that a rotatable prism and a substantially flat surface inclined at the prism tip of the second optical path conversion means are non-parallel. By being non-parallel, the optical path can be prevented from being attenuated, and a good three-dimensional image with high resolution can be obtained.
- the second optical path changing means is a prism having a substantially spherical surface inclined at the tip, or a ball lens having a substantially flat reflecting surface in a part of a substantially hemispherical shape.
- FIG. 1 is a cross-sectional view of a probe for three-dimensional scanning optical imaging according to an embodiment of the present invention.
- a fixed-side optical fiber 1 for guiding a light beam from the rear end side to the front end side of the probe is a sufficiently long tube-like catheter 6. It is inserted through the approximate center inside.
- Rotation side optical fiber 2 is rotatably provided at the tip side of fixed side optical fiber 1.
- a first optical path changing means 3 (in the figure, 3a or 3b depending on the position, for example, a prism having a shape obtained by cutting both surfaces of a substantially cylindrical transparent body with a substantially non-parallel plane) Is rotated by the first motor 12 independently of the rotation-side optical fiber 2 and the first optical path changing means 3 is rotated, so that the light beam is, for example, an angle of ⁇ 1 + ⁇ 2 with respect to the axis in the figure. It is configured to radiate and rotate forward.
- the light beam transmitted through the fixed-side optical fiber 1 is condensed at the tip of the rotation-side optical fiber 2 and rotated toward the first optical path changing means 3 with a minute angle ( ⁇ 1) with respect to the axis while rotating.
- a second optical path changing means 20 for radiating is attached.
- the second optical path changing means 20 is formed by combining a conical condensing lens 20c and a prism 20a.
- the rotation-side optical fiber 2 and the fixed-side optical fiber 1 are opposed to each other with a minute distance of about 5 ⁇ m (micron), and the rotating light connector 22 includes the rotating light shielding plate 5 and the optical fiber fixture 4. End surfaces of the rotation-side optical fiber 2 and the fixed-side optical fiber 1 are processed smoothly, and a high transmittance can be maintained between the rotation-side optical fiber 2 and the fixed-side optical fiber 1, and the optical connection is made with almost no loss.
- the first motor 12 is built in the catheter 6, the rotor magnet 11 is attached, and the hollow rotary shaft 10 supported by the first bearings 9a and 9b rotates.
- a voltage is applied to the motor coil 7 through the electric wire 23 to the first motor 12, and the first optical path changing means 3 is attached to the holder portion 10 a of the hollow rotary shaft 10 and rotated.
- the second rotating shaft 13 supported by the second bearings 18 a and 18 b is lightly press-fitted into a hole formed in the approximate center of the vibration element 14, and the second rotation is performed by the elasticity or spring property of the vibration element 14.
- a stable frictional force is generated between the shaft 13 and the shaft 13.
- the second rotating shaft 13 of the second motor 19 fixes the rotation-side optical fiber 2 in the center hole, and a voltage is applied to the pattern electrode 16 and the electrostrictive element 15 through the wired electric wire 17, and the second optical path conversion means 20.
- the vibrating element 14 is prevented from rotating with respect to the motor case 8.
- the electric wire 17 functions to prevent rotation.
- the first motor 12 is provided with first pulse generating means 25 comprising a rotating member 25a and a fixed member 25b shown in FIG. 2, and similarly, the second motor 19 has a rotating member 24a and a fixed member shown in FIG.
- a second pulse generating means 24 comprising 24b is provided, and generates a pulse signal once per rotation or a plurality of times according to the rotation of the first and second motors, respectively.
- the generation principle of these pulses is a magnetic sensor such as an induction coil or a Hall element, or an optical sensor using an optical shutter and an optical sensor.
- a translucent member 21 capable of transmitting a light beam is attached to the catheter 6 in front of the first optical path changing means 3 from which the light beam is radiated.
- the translucent member 21 is formed with a substantially spherical surface portion 21a as necessary.
- the spherical surface portion 21a has a constant thickness as required, and the thickness is changed to provide a lens function.
- the translucent member 21 is made of a transparent resin, glass, or the like, and is coated with a coating or the like for reducing surface reflection and minimizing total reflection of light rays and increasing transmittance as necessary.
- a CCD camera unit 83 is attached to the distal end observation unit 84 of the guide catheter 82, and a tubular catheter 6 is inserted into a through hole 81 called a forceps channel.
- a light beam such as a near infrared ray or a laser beam emitted from a light source in the main body 85 passes through the fixed-side optical fiber 1 in the catheter 6 in the guide catheter 82.
- the light beam is emitted from the fixed-side optical fiber 1 through the rotating optical connector 22 and radiated to the rotating-side optical fiber 2 ⁇ second optical path converting means 2 ⁇ first optical path converting means 3a.
- the near-infrared ray further passes through the translucent part 21, passes through the skin of the object to be inspected to about 2 to 5 millimeters, and the light reflected from the near-infrared ray passes through the same optical path as above in the reverse direction.
- Optical path changing means 3a ⁇ second optical path changing means 20a ⁇ rotation side optical fiber 2 ⁇ rotation optical connector 22 ⁇ fixed side optical fiber 1 is passed to the optical interference analysis unit 88.
- the thickness of the surface layer 27a and the presence / absence of internal defects are observed in a three-dimensional image by emitting light rays in the back of the deep hole 27 of the subject 26.
- the electric power is supplied from the electric wire 23, and the first motor 12 rotates at a constant speed in the range of about 1800 to 20,000 rpm.
- the light beam guided from the fixed-side optical fiber 1 is the rotating optical connector 22 and the rotating-side optical fiber. 2, emitted from the second optical path changing means 20 a, reflected by the substantially flat surface portion of the first optical path changing means 3 a, and changed in direction to a certain angular direction (downward angle ⁇ 1 + ⁇ 2 indicated by an arrow in FIG. 1). Radiated and rotated.
- the radiation direction of the light beam is greatly bent with respect to the axis, and the radiation angle is downward ( ⁇ 1 + ⁇ 2).
- the angle ⁇ 1 180 degrees of the first pulse generating means 24 of the first motor 12 and the angle of the second pulse generating means 24 of the second motor 22 are also 180 degrees, and the phase difference between these two angles ( ⁇ 1 ⁇ ⁇ 2) is the same as FIG. 4 and is 0 degree.
- the radiation direction of the light beam is greatly bent with respect to the axis, and the radiation angle is an upward direction of ( ⁇ 1 + ⁇ 2).
- the angle Q of the substantially planar portion of the first optical path conversion means 3b and the angle S of the surface of the prism 20d of the second optical path conversion means 20 are never parallel surfaces and have an angle of, for example, 5 degrees or more. ing. This is because, if this becomes a parallel plane, the OCD image obtained by total reflection of the light beam may deteriorate. If the first and second optical path conversion units are designed so that the phase difference ( ⁇ 1 ⁇ 2) of the rotation angles of the first and second optical path conversion units is 0 degrees and the first and second optical path conversion units are not parallel, the first and second optical path conversion units There is no fear of parallelism between the first and second optical path changing means, and a good image can be obtained.
- FIG. 5 illustrates a state in which the phase angle is changed by changing the rotation speeds of the first optical path conversion unit 3a and the second optical path conversion unit 20a.
- the light beam emitted from the second optical path changing means 20b at an angle with respect to the axis is reflected by the substantially flat portion of the first optical path changing means 3a and returns in the opposite angular direction, with the result that the light ray is almost The light is rotated and radiated on the axis almost parallel to the axis.
- the angle phase difference ( ⁇ 1 ⁇ 2) is +180 degrees.
- the radiation angle of the light beam is ( ⁇ 1 + ⁇ 2) ⁇ 0 degrees.
- FIG. 6 illustrates a state in which the first optical path conversion unit 3a and the second optical path conversion unit 20a are rotated from the state of FIG.
- the light beam emitted from the second optical path changing means 20a at an angle with respect to the axis is reflected by the substantially plane portion of the first optical path changing means 3b and returns in the opposite angular direction, so that the light ray is almost It is rotated and radiated on the axis almost parallel to the axis.
- the angle ⁇ 1 180 degrees of the first pulse generating means 24 of the first motor 12 and the angle of the second pulse generating means 24 of the second motor 22 are 0 degrees due to a delay in rotation.
- the phase difference ( ⁇ 1 ⁇ 2) is +180 degrees.
- the radiation angle of the light beam is ( ⁇ 1 + ⁇ 2) ⁇ 0 degrees as in FIG.
- FIG. 7 illustrates the rotational phase angle ( ⁇ 1 ⁇ 2) described with reference to FIGS. 1 to 6 and the radiation direction of the light beam forward.
- the irradiation direction changes depending on the phase difference ( ⁇ 1 ⁇ 2) between the angle ⁇ 1 of the first pulse generation means 24 of the first motor 12 and the angle ⁇ 2 of the second pulse generation means 24 of the second motor 22, and the light beam is forward. Without escaping toward the area radiated to the range indicated by the radius R in the figure.
- FIG. 8 is a three-dimensional representation of the radiation range of light rays. Since the light beam is focused so as to be focused at the front L of the catheter 6, it is emitted in a substantially conical shape indicated by an angle ( ⁇ 1 + ⁇ 2) within the radius R in the figure, and the subject is three-dimensionally radiated. Scanning.
- a light beam such as a near infrared ray or a laser further passes through the light transmitting part 21 in FIG. 1 and passes through the subject surface to about 2 to 5 mm (millimeters), and the light reflected from the light is converted from the light transmitting part 21 to the first optical path conversion.
- Means 3 ⁇ second optical path changing means 20 ⁇ rotation side optical fiber 2 ⁇ rotation optical connector 22 ⁇ fixed side optical fiber 1 is passed to the optical interference analysis unit 88.
- FIG. 11 is a pulse timing chart generated by the first motor 12 and the second motor 19 of the optical invention imaging probe.
- the upper diagram in the figure shows the generation from the first pulse generating means 25 of the first motor 12.
- the pulse, the lower diagram in the figure shows the pulse generated by the second pulse generating means 24 of the second motor 19, and the horizontal axis shows the time axis.
- the time zone indicated by Stand by in the figure is a state in which the first motor 12 and the second motor 19 are waiting for a scanning start signal while rotating at the same rotational speed.
- the first motor 12 rotates at a speed represented by, for example, N pulses / second (for example, 30 rotations / second) and the subject.
- the OCT observation image data is started to be accumulated in the computer 89.
- the second motor 19 rotates at a speed of, for example, (N-1) pulses / second (for example, 29 rotations / second), so that the radiation angle is 0.5 seconds from ⁇ 1 to ⁇ 2, as shown in FIG. After 1 second, the angle returns to ⁇ 1 again, completing the three-dimensional emission of light.
- the computer captures a total of twice (one set for two times) of three-dimensional data within a time when the radiation angle is reciprocated between ⁇ 1 and ⁇ 2, and obtains a clear three-dimensional OCT diagnostic image.
- the first motor 12 and the second motor 19 are again in the Stand-by state, and rotate while waiting for the next Start signal.
- a more practical use of the OCT probe for three-dimensional scanning of the present invention is, for example, in the first stage, where the OCT probe of the present invention is fed into a long blood vessel.
- the first motor 12 and the second motor are used.
- the OCT probe of the present invention continues to perform two-dimensional 360-degree scanning while 19 rotates at the same rotation speed, and specifies the position of the affected part near the blood vessel in the human body from the two-dimensional image displayed on the monitor 90.
- the two-dimensional image is captured by using the pulse signals from the first pulse generating means 25, 25a, and 25b of FIG. 2 as a trigger and displayed on the monitor 90 by computer processing.
- the pushing and pulling of the OCT probe is stopped, the catheter 6 is stopped, and the second motor 19 is rotated at a speed of, for example, (N-1) pulses / second (for example, 29 rotations / second).
- the OCT apparatus can display a high-resolution three-dimensional image on the monitor 90 and perform detailed observation of the affected area.
- 3D image capture is triggered by the moment when both the pulse signals from the first pulse generating means 25, 25a and 25b and the pulse signals from the second pulse generating means 24, 24a and 24b shown in FIG. In this way, it is taken into the computer 89 and displayed on the monitor 90.
- the OCT probe of the present invention is further moved to the other end.
- the OCT probe of the present invention is rotated while the first motor 12 and the second motor 19 are rotated at the same rotational speed.
- the two-dimensional 360-degree scanning is continuously performed, and a two-dimensional OCT image is displayed on the monitor 90.
- the fixed-side optical fiber 1 is not rotated inside the long catheter 6 inside the entire length from the rear to the distal end of the catheter 6, so that it does not rub and can prevent occurrence of rotation transmission delay, torque loss, and the like.
- the rotation side optical fiber 2 is also rotatably arranged in the hole of the hollow rotary shaft 1 and there is no sliding loss, so that the rotation unevenness of the motor 12 is very small.
- the performance of the rotation speed is expressed by a rotation angle as a percentage in a general evaluation scale, but a high performance of 0.01% can be achieved in the present invention.
- the rotation unevenness of the endoscope probe of the conventional type in which the optical fiber is rubbed has only obtained a bad performance of about 100 times or more.
- FIG. 12 is an explanatory diagram of deep hole scanning of the optical imaging probe of the present invention.
- the catheter 6 enters the deep hole and the film thickness of the surface layer 28 is reached in the scanning range 29. Measurement, stereoscopic observation of the internal structure, observation of the presence or absence of internal defects, and the like.
- FIG. 13 is a cross-sectional view of the second motor 19 of the optical imaging probe. There is a sufficient space between the vibrator 14 inside the catheter 6 and the motor case 8, and the electric wire 23 and the electric wire 17 are arranged in this space. In this way, the wiring of the first motor 12 and the second motor 19 can be made space-efficient and compact.
- FIG. 14 is an explanatory diagram of a modified application example of the second optical path changing means of the optical imaging probe.
- the second optical path changing means 120 is a prism having a substantially spherical surface 120a inclined at the tip. According to this configuration, the second optical path conversion unit 120 can exhibit a sufficiently high light transmittance and condensing performance, and a compact three-dimensional observation image with high spatial resolution can be obtained.
- FIG. 15 is an explanatory diagram of a modified application example of the second optical path changing means of the optical imaging probe.
- the second optical path changing means 220 is composed of a condensing lens 220c, a first prism 220d, and a second prism 220e, and is cylindrical. Is housed in a cover 220f. According to this configuration, the second optical path conversion unit 220 can tilt the light beam to a sufficiently large angle, and can obtain a wide range of three-dimensional observation images.
- the most important required performance in the OCT three-dimensional operation image diagnostic apparatus of FIG. 10 is to obtain a three-dimensional image and to increase the spatial resolution of the three-dimensional image.
- the factor for achieving the spatial resolution includes the motor 12. Rotation speed unevenness, deflection accuracy of the hollow rotating shaft 10, accuracy and surface roughness of the first optical path conversion element 3 and the second optical path conversion means 20, and the like.
- the influence of the motor 12 is greatly affected by the rotational speed unevenness of the motor 12, and therefore the endoscope probe of the present invention incorporates the motor 12 at the tip and rotates the optical path conversion element with high accuracy and without rotational speed unevenness. Then, for example, a high three-dimensional spatial resolution of 10 microns or less can be stably achieved.
- the optical fiber since the optical fiber does not rotate relatively in a catheter such as an endoscopic device, the optical fiber is not rubbed, and generation of rotation transmission delay, torque loss, etc. is reduced, and high spatial resolution of 10 microns or less.
- a clear OCT analysis image can be obtained, and a light beam can be emitted in a certain range in the axial direction by intentionally changing the thickness of the second optical path changing means, so that a three-dimensional observation image can be obtained.
- the three-dimensional scanning optical imaging probe of the present invention has a high-accuracy rotational scanning mechanism by providing optical path conversion means that rotates without speed unevenness by a motor near the tip of the tube without rotating the optical fiber in the long tube.
- a high-accuracy rotational scanning mechanism by providing optical path conversion means that rotates without speed unevenness by a motor near the tip of the tube without rotating the optical fiber in the long tube.
- the spatial resolution which is the basic performance of the OCT diagnostic imaging apparatus
- the front three-dimensional scanning enables three-dimensional observation of the bottom of the deep hole, and can be applied to an industrial OCT diagnostic apparatus.
- it is expected to be used for diagnosis and treatment of minute lesions at medical sites.
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Abstract
Description
この構成によれば、内視鏡装置等のカテーテル内で光ファイバーが擦れることがなく、回転伝達遅れやトルク損失等の発生が軽減される。更に第1光路変換手段と第2光路変換手段のそれぞれが独立して回転することで光線を前方の3次元領域に放射が行え、近赤外光又はレーザ光等を用いるOCT内視鏡において空間分解能が高い3次元の観察画像を得ることができる。
この構成によれば、第1光路変換手段の後方に第1モータ及び第2モータを配置できるので、前方へ放射される光線がモータやモータの電線が障害にならずに放射できるため、広範囲で陰の無い前方の3次元走査が可能である。
この構成によれば、光線が第1光路変換手段を透過するとともに、広範囲な前方の3次元走査が可能である。
この構成により、光線が第2光路変換手段により集光され、かつ透過し、さらに回転中心に対して光路を微小角度傾けて回転放射することができる。
この構成によれば、第1光路変換手段、及び第2光路変換手段の回転角度の組合せにより、光線を前方の広範囲に放射することができる。
この構成により前記第2光路変換手段は広い角度範囲に光線を放射することができる。
非並行であることにより、光路の減衰が防止でき分解能が高い良好な3次元画像が得られる。
この構成により、装置がコンパクトに構成できる。
図1は本発明の実施の形態に係る3次元走査型光イメージング用プローブの断面図であり、プローブの後端側から先端側に光線を導く固定側光ファイバー1は十分に長いチューブ状のカテーテル6の内部の略中心に挿通されている。
この状態では、光線の放射方向は軸線に対して大きく曲げられており、放射角度は、(θ1+θ2)の下向きになる。
図5において、第2光路変換手段20bから軸線に対して角度をもって放出された光線は、第1光路変換手段3aの略平面部で反射し逆の角度方向に方向を戻し、その結果光線はほぼ軸線上を軸線とほぼ平行に回転放射される。この時、第1モータ12の第1パルス発生手段24の角度α1=0度、第2モータ22の第2パルス発生手段24の角度は回転に遅れが生じて-180度であり、これら2つの角度の位相差(α1-α2)は+180度になっている。この状態では、光線の放射角度は、(θ1+θ2)≒0度になる。
図6において、第2光路変換手段20aから軸線に対して角度をもって放出された光線は、第1光路変換手段3bの略平面部で反射し逆の角度方向に方向を戻し、その結果光線はほぼ軸線上を軸線とほぼ並行に回転放射される。この時、第1モータ12の第1パルス発生手段24の角度α1=180度、第2モータ22の第2パルス発生手段24の角度は回転に遅れが生じて0度であり、これら2つの角度の位相差(α1-α2)は+180度になっている。この状態においても光線の放射角度は、図6と同様に(θ1+θ2)≒0度になる。
図中Stand byに示す時間帯は、第1モータ12と第2モータ19が同一の回転数で回転しながら走査開始信号を待っている状態である。
次に第2段階ではOCTプローブの押し引きを中止し、カテーテル6を静止させ、第2モータ19に、例えば(N-1)パルス/秒(例えば29回転/秒)の速度で回転さえて光線の3次元放射を行い、OCT装置はモニタ90に分解能の高い3次元画像を表示する事ができ、患部の詳しい観察を行うものである。
装置機械において、被検体26に深穴27があり、さらにそれら表面が表面層28で覆われている場合等に、カテーテル6は深穴に進入し走査範囲29において、表面層28の被膜厚さの測定、及び内部組織の立体観察、内部欠陥の有無の観察等が行える。
カテーテル6の内部の可振子14とモータケース8の間には十分な空間があり、この空間に電線23と電線17が配置されている。このようにして第1モータ12、第2モータ19の配線はスペース効率良く、コンパクトに行える。
この構成によれば、第2光路変換手段120が十分に高い光線の透過率と集光性能を発揮することができ、コンパクトで空間分解能が高い3次元の観察画像を得ることができる。
この構成によれば、第2光路変換手段220は、光線を十分に大きい角度に傾ける事が可能であり、広範囲な3次元の観察画像を得ることができる。
2 回転側光ファイバー
3、3a、3b 第1光路変換手段(プリズム)
4 光ファイバー固定具
5 遮蔽板
6 カテーテル(チューブ)
7 モータコイル
8 モータケース
9a、9b 第1軸受
10 中空回転軸
10a ホルダー部
11 ロータ磁石
12 第1モータ
13 第2回転軸
14 可振子
15 電歪素子
16 パターン電極
17、23 電線
18a、18b 第2軸受
19 第2モータ
20、20a、20b、120、220 第2光路変換手段
20c、220c 集光レンズ
20d、120a、220d、220e プリズム
21 透光部材
21a 球面部
22 回転光コネクター(光ロータリコネクター)
24、24a、24b 第2パルス発生手段
25、25a、25b 第1パルス発生手段
26 被検体
27 深穴
28 表面層
29 走査範囲
81 鉗子チャネル
82 ガイドカテーテル
83 CCDカメラ部
84 先端観察部
85 本体
86 第1モータドライバ回路
87 第2モータドライバ回路
88 光干渉解析部
89 コンピュータ
90 モニタ
220f カバー
Claims (8)
- 先端側に入射した光を後方側へ導く光イメージング用プローブにおいて、
回転不能に配置され略チューブ状のカテーテルに内蔵された固定側光ファイバーと、
前記固定側光ファイバーの先端側に位置し、第1モータにより回転駆動させられ、光線を回転中心に対して角度を傾けて前方に回転放射する第1光路変換手段と、
前記固定側光ファイバーと、前記第1光路変換手段の間に位置し、回転光コネクターにより光学的に接続され、第2モータにより回転駆動される回転側光ファイバーと、
前記回転側光ファイバーの先端側に、回転中心に対して光路を微小角度傾けて回転放射し、光線を前記第1光路手段に照射する第2光路変換手段を、略同一線上に配置し、
光線を前記固定側光ファイバーから、前記回転光コネクター、前記第2光路変換手段、前記第1光路変換手段の順に透過させ、前方に放射させることを特徴とする光イメージング用プローブ。
- 前記第1モータの回転軸は中空形状であり、第1光路変換手段が固定されると共に、中空穴に前記回転側光ファイバーが回転自在に貫通すると共に、
前記第2モータの回転軸も中空形状であり、この穴に前記回転側光ファイバーを固定して回転させることを特徴とする請求項1記載の光イメージング用プローブ。
- 前記第1光路変換手段は回転可能なプリズムであることを特徴とする請求項1又は請求項2記載の光イメージング用プローブ。
- 前記第2光路変換手段は先端に傾斜する略平面を有するプリズムであることを特徴とする請求項1から3何れか1項記載の光イメージングプローブ。
- 前記第1モータの回転角に応じて少なくとも1回転に1回以上のパルスを発生する第1パルス発生手段と、前記第2モータの回転角に応じて少なくとも1回転に1回以上のパルスを発生する第2パルス発生手段を有し、第1及び第2のパルス発生手段からのパルスにより第1及び第2モータの回転速度を調整する制御手段を有し、第1モータの回転速度N1と第2モータの回転速度N2の関係を、N2=N1-X[回転/秒]で回転させることで、第1光路変換手段からN1[回転/秒]の回転速度で前方に放出させる共に、X[往復/秒]の速度で光線の回転中心に対する放出角を変化させることを特徴とする請求項1から4何れか1項記載の光イメージング用プローブ。
- 前記第2光路変換手段は、集光レンズと第1プリズムと第2プリズムとを、略一直線上に配置したことを特徴とする請求項1から5何れか1項記載の光イメージングプローブ。
- 前記第1光路変換手段は、回転可能なプリズムと前記第2光路変換手段のプリズム先端に傾斜する略平面とが非平行である請求項1から6何れか1項記載の光イメージングプローブ。
- 前記第2光路変換手段は先端に傾斜する略球面を有するプリズムであるか、または略半球形状の一部に略平面の反射面を有するボールレンズであることを特徴とする請求項1から7何れか1項記載の光イメージングプローブ。
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