JP4021975B2 - Optical scanning probe device - Google Patents

Optical scanning probe device Download PDF

Info

Publication number
JP4021975B2
JP4021975B2 JP23300197A JP23300197A JP4021975B2 JP 4021975 B2 JP4021975 B2 JP 4021975B2 JP 23300197 A JP23300197 A JP 23300197A JP 23300197 A JP23300197 A JP 23300197A JP 4021975 B2 JP4021975 B2 JP 4021975B2
Authority
JP
Japan
Prior art keywords
mode fiber
light
optical scanning
scanning probe
single mode
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Fee Related
Application number
JP23300197A
Other languages
Japanese (ja)
Other versions
JPH1156786A (en
Inventor
武文 上杉
仁士 上野
克一 今泉
謙二 吉野
章弘 堀井
義直 大明
正弘 大野
英治 安田
剛志 小澤
広之 山宮
勇実 平尾
純 広谷
均 水野
利昌 河合
栄 竹端
守 金子
秀道 青木
Original Assignee
オリンパス株式会社
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by オリンパス株式会社 filed Critical オリンパス株式会社
Priority to JP23300197A priority Critical patent/JP4021975B2/en
Priority claimed from US09/141,430 external-priority patent/US6069698A/en
Priority claimed from US09/141,572 external-priority patent/US6327493B1/en
Publication of JPH1156786A publication Critical patent/JPH1156786A/en
Application granted granted Critical
Publication of JP4021975B2 publication Critical patent/JP4021975B2/en
Anticipated expiration legal-status Critical
Application status is Expired - Fee Related legal-status Critical

Links

Images

Description

[0001]
BACKGROUND OF THE INVENTION
The present invention relates to an optical scanning probe device that is inserted into a forceps channel of an endoscope and scans low interference light to obtain a tomographic image of a subject inside a body cavity.
[0002]
[Prior art]
In recent years, when diagnosing a living tissue, in addition to an imaging device that obtains optical information on the surface state of the tissue, an optical CT device that can obtain optical information inside the tissue has been proposed.
[0003]
This optical CT apparatus uses a picosecond pulse to detect information inside the living body and obtain a tomographic image. However, a laser light source that generates ultrashort pulse light on the order of picosecond pulses is expensive and large in size, and is difficult to handle.
[0004]
Recently, interferometric OCT (optical coherence tomography) that obtains a tomographic image of a subject using low coherence light has been disclosed in, for example, Japanese Patent Application Laid-Open No. 6-511312.
[0005]
[Problems to be solved by the invention]
In this conventional example, no detailed disclosure is made for use in a body cavity. Although a simple scanning mechanism is disclosed, there is a description such as incorporation into a part of an endoscope when used in a body cavity, but a detailed scanning mechanism is not disclosed.
[0006]
In addition, in order to be able to be used while observing with an endoscope, a device that can be used by being inserted through the forceps channel of the endoscope and has a mechanism for performing stable optical scanning in that state is used. It can be used in combination with a endoscope, and the application range can be expanded, which is desirable.
However, the above-described conventional example does not disclose a detailed scanning mechanism that can be used by being inserted through the forceps channel of the endoscope and that stably scans low interference light.
In principle, it is possible to obtain a tomographic image by manually moving an optical probe that can be inserted into the forceps channel of an endoscope and does not have a scanning mechanism, but there is no mechanism for detecting the amount of movement. The tomographic image in the scanning direction cannot be displayed.
[0007]
(Object of invention)
The present invention has been made in view of the above points, and an object thereof is to provide an optical scanning probe apparatus that can be inserted into a channel of an endoscope and can obtain a tomographic image by scanning with low interference light. To do.
[0008]
[Means for Solving the Problems]
  To achieve the above objectiveClaim 1The optical scanning probe deviceAn optical scanning probe device for an optical imaging apparatus that irradiates a subject with low coherence light and constructs a tomographic image of the subject from information of light scattered in the subject, and is disposed in a forceps channel of an endoscope Can be inserted,The tip isClosedSlender and flexible cylinderAnd is formed inAt least the side surface on the tip side is provided with a sheath formed of a material having good light transmissivity, and is rotatably provided around the longitudinal axis inside the sheath,A rotational force is applied by the rotational drive device.FlexibleNaThe shaft and the flexibleNaInside the shaftAlong the central axis of the sheathSingle mode file providedWith,The low-coherence light having an effective diameter which is provided on the rear end side of the single-mode fiber and is smaller than the light beam diameter of the incident low-coherence light is incident on the rear end of the single-mode fiber.A lens,The single mode fiber is disposed on the tip side, rotated by the shaft to which a rotational force is applied, and guided by the single mode fiber.Change the light pathLightAnd a path changing means.
[0009]
DETAILED DESCRIPTION OF THE INVENTION
Embodiments of the present invention will be described below with reference to the drawings.
(First embodiment)
1 to 6 relate to a first embodiment of the present invention. FIG. 1 shows a configuration of an optical tomographic image apparatus (optical imaging apparatus) including the first embodiment, and FIG. 3 shows an endoscope through which the embodiment is inserted, FIG. 3 shows a rear end side portion of the optical scanning probe apparatus according to the first embodiment of the present invention, and FIG. 4 shows an overall configuration of the optical scanning probe apparatus. 5 shows a front end side portion of the optical scanning probe device, and FIG. 6 shows a structure in which a part of the connector portion is changed.
[0010]
An optical tomographic image apparatus 1 shown in FIG. 1 has a low coherence light source 2 such as an ultra-high brightness light emitting diode (hereinafter abbreviated as SLD). The low-coherence light source 2 has a feature of low-coherence light that exhibits coherence only in a short distance range in which the wavelength is, for example, 1300 nm and the coherence distance is, for example, about 17 μm. In other words, for example, when this light is branched into two and then mixed again, if the difference between the two optical path lengths from the branched point to the mixed point is within a short distance range of about 17 μm, it is regarded as interfering light. When it is detected and the optical path length is longer than that, it shows a characteristic that does not interfere.
[0011]
The light of the low coherence light source 2 is incident on one end of the first single mode fiber 3 and transmitted to the other end face (tip face) side.
The first single mode fiber 3 is optically coupled to the second single mode fiber 5 at an intermediate optical coupler 4. Accordingly, the optical coupler 4 is branched into two and transmitted.
[0012]
An optical rotary joint 6 that performs coupling capable of transmitting light between the non-rotating part and the rotating part is inserted at the tip side of the first single mode fiber 3 (from the optical coupler part 4). An optical scanning probe device (hereinafter abbreviated as an optical scanning probe) 8A of the first embodiment is inserted into the fourth single mode fiber 9 that is rotationally driven through the third single mode fiber 7 of the first embodiment. Light from the low interference light source 2 is transmitted (guided).
[0013]
The transmitted light is irradiated while being scanned from the distal end side of the optical scanning probe 8A to the living tissue 11 side. Further, a part of the reflected light scattered on the surface or inside of the living tissue 11 side is taken in, returns to the first single mode fiber 3 side through the reverse optical path, and part of it is reflected by the optical coupler unit 4. It moves to the second single mode fiber 5 side, and is incident on, for example, a photodiode 12 as a photodetector from one end of the second single mode fiber 5. The rotor side of the optical rotary joint 6 is rotationally driven by the rotational drive device 13.
[0014]
Further, an optical loop portion 14 is provided in the middle of the second single mode fiber 5 from the optical coupler portion 4 to the distal end side, and an optical path length variable mechanism 15 is provided at the distal end thereof.
[0015]
In other words, the lens 16 and the mirror 17 are disposed so as to face the distal end surface of the second single mode fiber 5, and the mirror 17 can change the optical path length by the actuator 18 as indicated by an arrow a. . The light reflected by the mirror 17 is mixed with the light leaked from the first single mode fiber 3 side by the optical coupler unit 4 and is received by the photodiode 12 together. The actuator 18 and the rotary drive device 13 are controlled by the control device 19.
[0016]
The loop portion 14 is set to have a length substantially equal to the optical path length of the fourth single mode fiber 9 or the like on the optical scanning probe 8 side. The optical path length reflected by the mirror 17 from the front end surface of the second single mode fiber 5 and returning to the front end surface of the second single mode fiber 5 is reduced from the front end surface of the fourth single mode fiber 9 by a microprism described later. The optical path length is irradiated to the side of the living tissue 11 and reflected by the inside of the living tissue 11 or the like so as to return to the distal end surface of the fourth single mode fiber 9.
[0017]
Then, by changing the position of the mirror 17 in the optical path length variable mechanism 15 on the reference light side and changing the optical path length, the reflected light at the depth position of the living tissue 11 having a value equal to the optical path length is obtained. Interference is made so that reflected light at other depths can be made non-interfering.
[0018]
The signal photoelectrically converted by the photodiode 12 is amplified by an amplifier 21 and then input to a demodulator 22. The demodulator 22 performs demodulation processing for extracting only the signal portion of the interfered light, and the output is input to the computer 24 via the A / D converter 23. The computer 24 generates image data corresponding to the tomographic image, outputs it to the monitor 25, and displays the OCT image 26 on the display surface.
[0019]
The computer 24 is connected to the control device 19, and the computer 24 performs variable control of the optical path length of the reference light via the control device 19 via the actuator 18 and control of the optical scanning direction by rotation by the rotation drive device 13. I have to.
[0020]
As shown in FIG. 2, the optical scanning probe 8 according to the first embodiment projects the distal end side of the optical scanning probe 8 from the distal end opening through the forceps insertion channel 28 from the forceps insertion opening 28 of the endoscope 27. it can.
[0021]
The endoscope 27 has an elongated insertion portion 29 so that it can be easily inserted into a body cavity, and a wide operation portion 30 is provided at the rear end of the insertion portion 29. A forceps insertion port 28 is provided near the front end of the insertion portion 30, and the forceps insertion port 28 communicates with a forceps insertion channel therein.
[0022]
A light guide (not shown) is inserted into the insertion portion 29, the incident end of the light guide is connected to the light source device, the illumination light is transmitted and emitted from the illumination window provided at the distal end portion of the insertion portion 29, and the affected part or the like. Illuminate. In addition, an observation window is provided adjacent to the illumination window, and an objective optical system is attached to the observation window so that an illuminated affected area or the like can be observed by the optical system.
[0023]
Then, under observation of the observation optical system at the distal end portion of the endoscope 27, low-interference light is irradiated by the optical scanning probe 8 </ b> A to the biological tissue 11 side of the target portion such as an affected part, and the inside of the biological tissue 11. The tomographic image data is obtained, and the OCT image 26 can be displayed on the display surface of the monitor 25.
[0024]
The configuration of the optical scanning probe 8A according to the first embodiment will be described below with reference to FIGS.
The tip end side of the first single mode fiber 3 is optically connected to the fourth single mode fiber 9 inserted into the optical scanning probe 8A via the third single mode fiber 7 in the optical rotary joint 6 shown in FIG. Is bound to.
[0025]
A rotor receiver 31 is provided at the tip of the first single-mode fiber 3, and a rotor 32 is fitted in a recess of the rotor receiver 31, and is rotated by two bearings 33 interposed therebetween. The child 32 is rotatably supported (relative to the rotor receiver 31 that is not rotated).
[0026]
The first single mode fiber 3 and the third single mode fiber 7 are inserted along the centers of the rotor receiver 31 and the rotor 32, respectively, and convex lenses 34 and 35 are respectively provided on the end faces where the fibers 3 and 7 face each other. It is arranged so that light can be efficiently transmitted between the non-rotated fiber 3 and the rotated fiber 7.
[0027]
The rotor 32 is connected to a pulley 38 of a motor 37 that constitutes the rotation drive device 13 via a belt 36, for example. Due to the rotation of the motor 37, the rotor 32 is also rotated as indicated by the arrow b, so that the third single mode fiber 7 is also rotated. The motor 37 is driven to rotate at a constant speed by a motor drive signal from the rotation control unit 39.
[0028]
A connector portion 41 provided at the rear end of the optical scanning probe 8A is connected to the front end of the rotor 32.
As shown in FIG. 4, in the optical scanning probe 8A, a fourth single mode fiber 9 is arranged along the central axis of an elongated and tube-shaped sheath 42 serving as a mantle tube. The end and the tip are fixed to the connector main body 43 and the tip main body 44, respectively, and the fourth single mode fiber 9 is covered with a flexible shaft 45 as a hollow and flexible rotational force transmitting member. The inner diameter of the flexible shaft 45 is slightly larger than the outer diameter of the fourth single mode fiber 9.
The fourth single mode fiber 9 has a core diameter of about 9 μm, for example.
[0029]
The sheath 42 is formed of a tube that is transparent (for low interference light) and has good light transmittance, such as polymethylpentene. Further, the flexible shaft 45 has flexibility by making the closely wound coils double or triple, and has a function of efficiently transmitting the rotation applied to one end to the other end. The rear end and the front end of the flexible shaft 45 are also fixed to the connector main body 43 and the front end main body 44.
[0030]
The sheath 42 is fixed to a cylindrical connector cover 46 that forms a connector portion 41 at the rear end of the sheath 42, and a cylindrical connector body 43 is inserted inside the connector cover 46 through two bearings 47 provided at two locations to be freely rotatable. It is supported by. The rear end of the fourth single mode fiber 9 is inserted into a hole provided in the central axis of the connector main body 43 and fixed with an adhesive or the like.
[0031]
A convex portion 48 is provided on the rear end surface of the connector main body 43, while a concave portion 49 that fits the convex portion 48 is provided on the front end surface of the rotor 32. And when the rotor 32 is rotated in a state where the two are abutted, the connector main body 43 is also rotated. This rotational force is applied to the rear end of the flexible shaft 45, transmitted to the tip of the flexible shaft 45, and the tip body 44 attached to the tip is rotated.
[0032]
As shown also in FIG. 5, the tip of the fourth single mode fiber 9 is inserted into a hole provided in the central axis of the tip body 44 and fixed with an adhesive or the like, and the front side of the tip surface of the fourth single mode fiber 9 A Selfoc lens (GRIN lens) 51 that condenses the light emitted from the tip of the fourth single mode fiber 9 at a predetermined position is fixed. A microprism 52 that changes the optical path by reflection is fixed to the front end surface of the GRIN lens 51 with an adhesive or the like.
[0033]
Then, the light guided by the fourth single mode fiber 9 and disposed at a predetermined distance from the distal end surface is collected by the GRIN lens 51, reflected by the microprism 52 in a right angle direction, and transparent sheath 42. The outgoing light 53 that is transmitted through and condensed outside (by low interference light) can be emitted. Then, at a condensing point where light is condensed at a predetermined distance, a light beam diameter of, for example, 10 μm to 30 μm is set.
[0034]
Note that the tip surface of the fourth single mode fiber 9 is cut obliquely to reduce the incidence of light reflected by the rear surface of the GRIN lens 51 on the tip surface. Further, an antireflection film 54 is provided by coating an antireflection member on the rear surface of the GRIN lens 51 and the front surface of the microprism 52 to reduce the occurrence of reflected light.
[0035]
The tip of the sheath 42 is hemispherical and closed. The optical scanning probe 8A of the present embodiment has an overall length L of about 2000 mm and a sheath diameter D of 2.4 mm.
[0036]
Next, the operation of this embodiment will be described.
By illuminating illumination light from an endoscope light source device (not shown) with a light guide of the endoscope 27, the living tissue 11 side is illuminated from the illumination window at the distal end portion of the insertion portion 29. The illuminated living tissue 11 is imaged on a solid-state imaging device by the objective optical system of the observation window, subjected to signal processing by a video processor, and then displays an endoscopic image on a display monitor.
[0037]
When displaying a tomographic image with low interference light, the optical scanning probe 8A is passed through the forceps insertion opening 28 of the endoscope 27 as shown in FIG. Project the tip of the.
[0038]
1 is connected to the rotor 32 at the front end of the optical rotary joint 6 to constitute the optical tomographic image apparatus 1 of FIG.
Then, the low interference light of the low interference light source 2 is incident on the rear end of the first single mode fiber 3, and this low interference light passes through the third single mode fiber 7 in the optical rotary joint 6 and enters the optical scanning probe 8A. Is incident on the rear end of the fourth single-mode fiber 9.
[0039]
The incident low interference light is guided by the fourth single mode fiber 9 and is emitted from the front end surface to the opposing GRIN lens 51 side as shown in FIG. 4 or FIG. The light is incident on the microprism 52 that is bonded and fixed to the front end surface of the GRIN lens 51, is totally reflected by the inclined surface, and the outgoing light 53 is emitted in a direction different from the traveling direction by 90 °, and the outgoing light 53 is emitted. Irradiation is performed on the side of the living tissue 11 in the direction.
[0040]
As shown in FIG. 3, the rotor 32 constituting the optical rotary joint 6 is connected to a pulley 38 attached to the rotating shaft of the motor 37 by a belt 36, so that the rotor 37 is rotated by rotating the motor 37 at a constant speed. 32 also rotates at a constant speed in the direction indicated by the arrow b, and the connector main body 43 in the connector portion 41 connected to the tip of the rotor 32 also rotates.
[0041]
Since the rear end of the flexible shaft 45 covering the fourth single mode fiber 9 is fixed to the connector main body 43, the flexible shaft 45 also rotates, and this rotation is also transmitted to the front end by the flexible shaft 45. . In this case, since the rear end of the fourth single mode fiber 9 is fixed to the central hole of the connector main body 43, the fourth single mode fiber 9 also rotates together with the flexible shaft 45.
[0042]
The tip main body 44 attached to the tip of the flexible shaft 45 and having the tip of the fourth single mode fiber 9 fixed in the central hole also rotates, and the GRIN lens 51 and the microprism 52 fixed to the tip main body 44 are also rotated. Since it rotates, the emitted light 53 shown in FIG. 4 or 5 scans radially in a direction perpendicular to the axis of the optical scanning probe 8A.
[0043]
Then, the surface of the living tissue 11 and the portion near the surface where the optical characteristics of the tissue are different (refractive index changing portion) are reflected and scattered in the tissue, and a part becomes an optical path opposite to that at the time of irradiation. The light enters the front end surface of the fourth single mode fiber 9 through the microprism 52 and the GRIN lens 51 and is transmitted to the rear end side.
[0044]
Then, the light enters the front end surface of the first single mode fiber 3 through the third single mode fiber 7 in the optical rotary joint 6, and a part of the light is coupled to the second single mode fiber 5 side by the optical coupler unit 4. At that time, it is mixed with light on the reference light side (light reflected by the mirror 17), received by the photodiode 12, and photoelectrically converted into an electric signal.
[0045]
After this signal is amplified by the amplifier 21, only the interference light component is extracted and detected by the demodulator 22. Then, it is converted into a digital signal and input to the computer 24.
[0046]
The computer 24 obtains tomographic image data in the depth direction of the living tissue 11 by changing the optical path length by the optical path length variable mechanism 15, and controls the rotary drive device 13 through the control device 19 to control the internal portion of the biological tissue 11. The motor 37 is rotated at a constant speed to obtain tomographic image data for one frame.
[0047]
In the computer 24, the tomographic image data obtained sequentially can be temporarily stored in an internal image memory, read out at a predetermined cycle, and displayed on the monitor 25 as a tomographic image or an OCT image 26 as shown in FIG.
[0048]
In the present embodiment, the fourth single mode fiber 9 disposed along the central axis of the optical scanning probe 8A is rotationally driven, and the GRIN lens 51 and the microprism 52 provided on the distal end side thereof are also rotationally driven, so that the light Low-interference light can be stably scanned in the direction perpendicular to the central axis of the scanning probe 8A. Therefore, the tomographic image in the depth direction can be stably obtained by spreading two-dimensionally in the circumferential direction.
[0049]
Specifically, for example, by performing circumferential scanning in such a narrow lumen inner wall portion to obtain a circumferential tomographic image, the observation of the surface state by the endoscope 27 and the surface including the surface by the tomographic image are obtained. Diagnosis such as detecting the nature of the internal lesion site can be performed effectively.
[0050]
As another use example, for example, in the case of observing a site of interest such as an affected part in the living tissue 11 in the body cavity with the endoscope 27 and mainly observing the internal state thereof, light is applied to the site of interest. Similarly, the side surface of the tip of the scanning probe 8A is brought close (for example, the side surface of the tip of the optical scanning probe 8A is made substantially parallel to the surface of the site of interest), and similarly, a tomographic image is obtained by circumferential scanning.
[0051]
Then, a narrow range including the region of interest may be displayed on the monitor 25 without displaying the tomographic image in the entire circumference direction at the time of display. In this case, the present invention can be applied even inside a wide lumen. The present invention can also be applied to a case where a detailed tomographic image of a part of a narrow lumen portion is obtained.
[0052]
Further, the rotational speed (in other words, the scanning speed) may be changed between obtaining a tomographic image for the entire circumference and obtaining a tomographic image for a part of the entire circumference.
[0053]
According to the present embodiment, the present invention can be widely applied to the existing endoscope 27 provided with the forceps channel, and by this application, in addition to the endoscopic image of the surface of the affected part or the like, the inside of the endoscope can be obtained by a stable optical scanning mechanism. Since a tomographic image can be obtained stably, an optical scanning probe 8A suitable for performing a more accurate diagnosis can be provided.
[0054]
In the connector portion 41 at the rear end of the optical scanning probe 8A, the rear end of the fourth single mode fiber 9 is configured to abut against the front end of the third single mode fiber 7. FIG. In this way, a structure in which a lens is inserted may be used.
[0055]
FIG. 6A shows a structure in the vicinity of the connector portion 41 at the rear end of the optical scanning probe 8B of the modification. In this modification, a lens 56 is provided facing the tip surface of the third single mode fiber 7 in the rotor 32, and the diameter of the light beam emitted from the tip surface of the third single mode fiber 7 is, for example, shown in FIG. Spread to D1 as shown in B).
[0056]
Further, a lens 57 is provided facing the rear end surface of the fourth single mode fiber 9 in the connector main body 43 so that light incident at the effective diameter D2 is incident on the front end surface of the fourth single mode fiber 9. In addition, the effective diameter D2 was made smaller than the light beam diameter D1. That is, D1> D2.
[0057]
By adopting the structure of this modification, the rear end face of the fourth single mode fiber 9 can be mounted even when the detachable connector portion 41 is attached to the front end of the rotor 32 with a slight deviation in the axial direction. Light having a constant effective diameter D2 is incident from the front end surface of the third single mode fiber 7 and reflected light from the rear end surface of the fourth single mode fiber 9 to the front end surface of the third single mode fiber 7. Can be transmitted to the tip surface of the third single-mode fiber 7.
[0058]
Accordingly, even when the optical scanning probe 8B having the detachable connector portion 41 at the front end of the rotor 32 has some variation in the connector portion 41 between products, the transmission characteristics of the low interference light may vary. Can be reduced. Other functions and effects are the same as those of the first embodiment.
[0059]
(Second Embodiment)
Next, a second embodiment of the present invention will be described with reference to FIGS. FIG. 7 shows an optical scanning probe 8C according to the second embodiment of the present invention, and FIG. 8 shows a connector section in the AA section of FIG.
[0060]
In the first embodiment, the fourth single mode fiber 9 is rotated together with the flexible shaft 45 in the sheath 42. However, in the optical scanning probe 8C of the present embodiment, the fourth single mode fiber 9 is rotated. It is a structure that does not.
[0061]
The connector portion 41 of the optical scanning probe 8C is the same as the connector portion 41 of the first embodiment, except that the rear end of the fourth single mode fiber 9 is not fixed to the connector main body 43. A cylindrical and hard ferrule 61 is provided at the rear end, and is supported rotatably via a bearing 62 provided between the outer peripheral surface of the ferrule 61 and the inner peripheral surface of the connector main body 43.
[0062]
Also on the rotor 32 side, the third single mode fiber 7 is provided with a ferrule so as to be rotatable with respect to the rotor 32 via a bearing (not shown). The ferrule receiver 63 (of the single mode fiber 9) is formed, and the ferrule 61 at the rear end of the fourth single mode fiber 9 is fitted and connected.
[0063]
As in the case of the first embodiment, the connector main body 43 is provided with a convex portion 48, and the rotor 32 is provided with a concave portion 49 that fits into the convex portion 48. The rotation is also transmitted to the tip side of the flexible shaft 45.
[0064]
In the first embodiment, the tip of the fourth single-mode fiber 9 is fixed to the tip main body 44. However, in this embodiment, the diameter of the center hole of the tip main body 44 is increased and the front end side thereof is increased. As in the first embodiment, the GRIN lens 51 is fixed, but on the rear end side, there is an axial blur prevention member 64 formed of a cylindrical member fixed to the tip of the fourth single mode fiber 9. It is loosely fitted. The distal end of the fourth single mode fiber 9 is thickened by the shaft anti-shake member 64.
[0065]
The diameter of the central hole of the tip body 44 is slightly larger than the outer diameter of the shaft shake preventing member 64, and the tip body 44 is rotatable with respect to the shaft shake preventing member 64 side.
The shaft shake preventing member 64 is formed of, for example, a tube having a small frictional resistance, specifically, a Teflon tube.
[0066]
Other configurations are the same as those of the first embodiment, and the same members are denoted by the same reference numerals, and the description thereof is omitted.
As an operation according to the present embodiment, in the first embodiment, the third single mode fiber 7 inside the rotor 32 is rotated together with the rotation of the rotor 32, but is not rotated (in the present embodiment).
[0067]
In the first embodiment, the connector main body 43 is rotated with the rotation of the rotor 32, and the fourth single-mode fiber 9 whose rear end is fixed to the connector main body 43 is also rotated with the flexible shaft 45 on the outer side. However, the connector main body 43 and the flexible shaft 45 are rotated (in the present embodiment), but the fourth single mode fiber 9 inside thereof is not rotated.
Other operations are the same as those in the first embodiment.
[0068]
In the present embodiment, the low interference light can be scanned in the circumferential direction similarly to the first embodiment without rotating the fourth single mode fiber 9 inserted into the optical scanning probe 8C. It is possible to more effectively prevent the fourth single mode fiber 9 that is very thin from being cut by rotation. Other effects are the same as those of the first embodiment.
[0069]
(Third embodiment)
Next, a third embodiment of the present invention will be described with reference to FIGS. FIG. 9 shows the structure of the tip side of the optical scanning probe according to the third embodiment of the present invention, FIG. 10 shows that a light shielding mark is provided on the tip side, and FIG. 11 shows that the light shielding mark is provided. An endoscopic image obtained by imaging the tip side of the optical scanning probe is shown, and FIG. 12 shows a tomographic image obtained using this optical scanning probe.
[0070]
The optical scanning probe 8D uses, for example, a superelastic alloy pipe 66 instead of the flexible shaft 45 in the first embodiment. The superelastic alloy pipe 66 is formed of, for example, a nickel-titanium alloy.
[0071]
Further, in the present embodiment, the sheath 42 has a circular tube shape, and a distal end thereof is opened, and the distal end opening is a hard member having a function of transmitting light and is cylindrical and has one end (base end) opened. The base end of the tip cap 67 whose end is formed in a hemispheric shape is fixed. The tip cap 67 is made of, for example, polymethylpentene, like the sheath 42, and has a higher hardness and is formed with higher accuracy.
In the present embodiment, the rear surface of the GRIN lens 51 is also obliquely cut.
[0072]
Further, in the present embodiment, as shown in FIG. 10, a light shielding mark 68 is provided by applying a paint such as black on a portion that becomes a reference direction. Therefore, when the distal end side is observed with an endoscope, the orientation can be known from the light shielding mark image 68 'in the endoscopic image 69 shown in FIG.
[0073]
Also, in the tomographic image 70 shown in FIG. 12, the direction in which the black mark 69 is provided is black and becomes the portion 68 ″ where no image is formed, so that the orientation can be known. Others are the same as in the first embodiment. It is the composition.
[0074]
As an operation according to the present embodiment, the processing accuracy of the portion that emits the low interference light can be improved by forming the portion that emits the low interference light on the distal end side of the sheath 42 with another member having higher hardness. For this reason, the thickness of the emitted part can be made more uniform than when integrally molded with the sheath 42, and the emitted low interference light can be easily set to a smaller spot diameter at the focal position. Therefore, the variation in resolution can be reduced.
[0075]
Further, by providing a light shielding mark 68 on the distal end side, when the distal end side of the optical scanning probe 8D is imaged by the endoscope 27, the reference of the optical scanning probe 8D is included in the endoscopic image 69 as shown in FIG. By observing the light shielding mark image 68 ′ indicating the direction of the reference direction, the reference direction can be simplified.
[0076]
Further, when this optical scanning probe 8D is used, a tomographic image 70 as shown in FIG. 12 can be obtained, and the reference direction in the scanning direction can be easily known from the linear portion 68 ″ where no image is formed. The other effects are the same as those of the first embodiment.
[0077]
(Fourth embodiment)
Next, a fourth embodiment of the present invention will be described with reference to FIG. FIG. 13 shows the distal end side of an optical scanning probe 8E according to the fourth embodiment of the present invention.
[0078]
This optical scanning probe 8E shown in FIG. 13 has a higher optical transmittance than the tip cap 67 in the optical scanning probe 8D of FIG. 9 (that is, a good optical transmission of low interference light with less loss). A quartz glass pipe 71 and a metal cap 72 (having characteristics) are used.
[0079]
The periphery of the GRIN lens 51 and the like is filled with a transparent liquid 73 such as glycerin. The transparent liquid 73 such as glycerin has a refractive index of the core of the fourth single mode fiber 9, the refractive index of the glass forming the GRIN lens 51 and the microprism 52 (approximately 1.5), or the refractive index of the quartz glass pipe 71. It is a transparent liquid having a refractive index close to the refractive index. The other configuration is the same as that of FIG.
[0080]
According to the present embodiment, by forming the emission portion of the low interference light with the quartz glass pipe 71, the transmission loss due to the low interference light can be reduced, and a tomographic image with a good S / N can be obtained. Become.
[0081]
Further, by filling the transparent liquid 73 at least around the part that emits light, the light spot at the point focused by, for example, the cylindrical quartz glass pipe 71 is anisotropic due to the difference in refractive index when not filling. Can reduce the effects of
[0082]
That is, in FIG. 13, the anisotropy that causes the light spot at the point focused by the cylindrical quartz glass pipe 71 to have different diameters (sizes) in the left-right direction and the direction perpendicular thereto is shown. The anisotropic characteristics can be reduced by the transparent liquid 73 close to the refractive index.
Moreover, it is possible to further reduce the fact that transmission is not effectively performed due to reflection due to the difference in refractive index. The refractive index of the transparent liquid 73 is preferably a value in the vicinity of 1.5, but may be a value in the range of at least 1.0 to 2.0.
[0083]
In addition, by using the metal cap 72, for example, in the case where the diagnosis by X-ray is also used, the position of the tip side of the optical scanning probe 8E can be surely known (the metal cap 72 is made of metal). For example, a metal such as stainless steel, which has a higher specific gravity than aluminum or the like and has a large opaque function against X-rays, is easier to identify.
The other functions and effects are the same as those of the third embodiment.
[0084]
FIG. 14 shows the distal end side of the optical scanning probe 8F of the first modification of FIG. In this optical scanning probe 8F, for example, in the optical scanning probe 8E of FIG. 13, a transparent pipe 71 ′ is used instead of the quartz glass pipe 71, a guide hole 74 is provided in a slightly longer metal cap 72 portion, and the guide wire 75 is passed therethrough. It is something that can be done.
[0085]
In FIG. 14, the GRIN lens 51 and the like are not filled with the liquid 73 such as glycerin, but may be filled. Further, the optical scanning probe 8F is not limited to that applied to the one shown in FIG. 13, and may be applied to the one shown in FIG. 9, for example.
[0086]
According to the first modified example, the guide wire 75 can be passed therethrough, so that the guide wire 75 is first passed through a thin lumen portion such as a bile duct as a guide. It is possible to easily introduce the distal end side of the optical scanning probe 8F. The other effects are almost the same as those of the fourth embodiment.
FIG. 15 shows the distal end side of the optical scanning probe 8G of the second modified example of FIG. In this optical scanning probe 8G, a suction tube is inserted into the sheath 42 to provide a suction conduit 76, which is opened near the distal end of the sheath 42 to provide a suction conduit opening 77.
[0087]
The proximal side of the suction conduit 76 is connected to a suction device 78 so that suction can be performed. Then, by performing a suction operation, a tomographic image can be obtained by tightly fixing to a living tissue 79 in a wide body cavity such as the stomach.
[0088]
According to this modification, when observing a tomographic image of the target biological tissue 79 in a wide body cavity such as the stomach, the suction conduit opening 77 is set near the biological tissue 79 for suction. By suctioning with the device 78, the distal end side of the optical scanning probe 8G can be tightly fixed to the living tissue 79 portion.
[0089]
Therefore, stable optical scanning can be performed in the tightly fixed state, and a stable tomographic image can be obtained.
The other effects are almost the same as those of the fourth embodiment.
[0090]
(Fifth embodiment)
Next, a fifth embodiment of the present invention will be described with reference to FIGS. FIG. 16 shows the distal end side of the optical scanning probe 8H according to the fifth embodiment of the present invention, and FIG. In this embodiment, a bending function is provided on the distal end side of the optical scanning probe 8H so that a tomographic image of a desired part can be easily obtained.
[0091]
In this optical scanning probe 8H shown in FIG. 16, a hard tip ring 81 is provided at the tip of the sheath 42, and a transparent pipe 71 ′ and a tip cap 72 are provided at the tip of the tip ring 81.
[0092]
Further, the sheath 42 is formed of a multi-lumen tube, and the two angle wires 82 are inserted through the lumen close to the outer periphery of the multi-lumen tube at a symmetrical position such that the sheath 42 rotates 180 degrees around the central axis. Each tip is fixed to the tip ring 81. Further, a heat shrinkable tube 83 is covered on the outer side of the sheath 42 up to a predetermined length behind the distal end of the sheath 42, and the hardness is higher than that of the soft portion 84 at the distal end of the sheath not covered with the heat shrinkable tube 83. A hard portion (or low flexible portion) 85 that is hardened (or low in flexibility) is formed.
[0093]
The proximal side of the angle wire 82 is fixed so as to be wound around a pulley or the like, for example, and a lever is provided on the pulley shaft to form a bending operation portion. Then, by pulling one angle wire 82 by rotating the lever, the flexible portion 84 is bent downward as shown by the solid line in FIG. 17, or the lever is rotated in the reverse direction. Thus, as shown by a two-dot chain line in FIG. The rest of the configuration is almost the same as that of the fourth embodiment.
[0094]
According to this embodiment, the distal end side of the optical scanning probe 8H protruded from the forceps channel of the endoscope 27 can be bent by the operation of the bending operation portion, so that it does not have a bending function. It is possible to guide the distal end side to a more desired part than the object, or to set it at a close position. The other effects are almost the same as those of the fourth embodiment.
[0095]
(Sixth embodiment)
Next, a sixth embodiment of the present invention will be described with reference to FIG. FIG. 18 shows the distal end side of an optical scanning probe 8I according to the sixth embodiment of the present invention.
In the present embodiment, the optical scanning is performed by providing a rotation driving means on the tip side of the optical scanning probe 8I.
[0096]
A single mode fiber 92 is inserted along, for example, a central axis in a cylindrical sheath 91 that forms an insertion portion of the optical scanning probe 8I, and the distal end side of the single mode fiber 92 is a hole in the center of a columnar distal end body 93. Is fixed with an adhesive or the like. The outer peripheral surface of the distal end body 93 is also fixed to the inner peripheral surface near the distal end of the sheath 91.
[0097]
An opening at one end (base end) of a cylindrical and rigid transparent pipe 94 is fixed to the opening at the distal end of the sheath 91, and a substantially hemispherical distal end cap 95 is attached to the opening at the other end (distal end) of the transparent pipe 94. It is attached and the tip side is closed.
[0098]
The stator portion of the ultrasonic motor 96 is fixed inside the tip cap 95, and the microprism 52 and the GRIN lens 51 are attached to the rotating rotor portion via a support base 97.
[0099]
Further, the lead wire 98 connected to the ultrasonic motor 96 is inserted through the sheath 91 and connected to a drive circuit (not shown) on the hand side. Then, by turning on the switch, a drive signal is supplied to the ultrasonic motor 96 and the rotor side of the ultrasonic motor 96 is rotated, whereby the microprism 52 and the GRIN lens 51 attached to the support base 97 are indicated by arrows. It can be rotated as shown. Then, the low interference light guided by the single mode fiber 92 and emitted from the front end surface thereof is collected by the GRIN lens 51 that is driven to rotate against the front end surface, and further reflected by the slope of the microprism 52. Thus, the light can be emitted radially in a direction perpendicular to the axis of the optical scanning probe 8I.
[0100]
In the present embodiment, the base end side of the optical scanning probe 8I is connected to the distal end of the first single mode fiber 3 without using the optical rotary joint 6 shown in FIG. can do.
[0101]
According to the present embodiment, the first mode fiber 92 inserted into the optical scanning probe 8I is rotated without rotating the GRIN lens 51 and the microprism 52 that are arranged opposite to the tip side thereof, thereby It is possible to obtain substantially the same operational effects as in the case of the embodiment and the like.
[0102]
Further, when the single mode fiber 92 is also rotated using a rotational force transmission member such as the flexible shaft 45, the forceps channel that is also bent in the endoscope insertion portion 29 that is bent and inserted into the body cavity. There is a possibility that it may be difficult to transmit the rotation on the hand side to the tip side without delay in the state of being inserted through the inside. In such a case, the amount of deviation between the rotation position on the hand side and the rotation position on the tip side changes.
[0103]
If the amount of deviation in this case is constant, there is almost no deterioration of the image quality, but if the amount of deviation occurs locally, that is, if the rotational speed changes according to the angle, it is necessary to make the image on the hand side. When the rotation position of the image is detected, the error increases, and the image quality of the resulting tomographic image deteriorates. In order to avoid this, it is necessary to detect the rotational position on the tip side.
[0104]
In the present embodiment, even when it is inserted into a bent body cavity, it is not affected by this (the ultrasonic motor 96 and the like are arranged at the distal end portion, so there is almost no change in load when rotationally driven. Thus, the rotation position can be detected from the drive signal without detecting the rotation position. Accordingly, it is possible to obtain a stable optical scanning and a stable tomographic image by the optical scanning as well as an effect of being able to be thinned with a simple configuration for a comparative hand.
[0105]
Further, the breakage of the single mode fiber 92 can be effectively prevented as compared with the case of rotating the single mode fiber 92 inserted into the optical scanning probe 8I.
[0106]
In FIG. 18, the GRIN lens 51 may be fixed to the tip body 93 side, only the microprism 52 may be attached to the support base 97, and only the microprism 52 side may be rotated by the ultrasonic motor 96. In this case, since the load to be rotated can be reduced, the ultrasonic motor 96 having a small rotational driving force can be used, and the size can be further reduced. Alternatively, higher speed optical scanning is possible.
[0107]
FIG. 19 shows the tip side of the optical scanning probe 8J according to a modification. In this modification, a stator portion of an ultrasonic motor 96 having a hole through which a single mode fiber 92 is passed is fixed to the distal end surface of the distal end body 93, and the microprism 52 and GRIN are connected to the rotor portion via a cylindrical support base 97. A lens 51 is attached.
[0108]
Further, a lead wire 98 connected to the ultrasonic motor 96 is passed through a lead wire insertion hole provided in the tip body 93. The other configuration is the same as that of the sixth embodiment. The operation and effect of this modification are almost the same as those of the sixth embodiment.
[0109]
(Seventh embodiment)
Next, a seventh embodiment of the present invention will be described with reference to FIG. FIG. 20 shows the distal end side of the optical scanning probe 8K according to the seventh embodiment of the present invention. This embodiment is suitable for obtaining a tomographic image by being inserted into a blood vessel.
[0110]
In the present embodiment, the optical scanning probe 8K is provided with a fluid conduit 101 in the sheath 42, similar to the optical scanning probe 8G in FIG. 15, and the fluid conduit 101 has an opening 102 at the side near the distal end of the sheath 42. It is open at.
[0111]
The end on the proximal side of the fluid conduit 101 is connected to a tank 103 in which physiological saline is stored, and the physiological saline in the tank 103 is opened through the fluid conduit 101 by driving the pump 104. 102 can be sent to the outside. The other configuration is the same as that of the optical scanning probe 8G of FIG.
[0112]
Therefore, when the optical scanning probe 8K is used to obtain a tomographic image by being inserted into the blood, it is difficult to obtain a tomographic image due to scattering by the blood. By injection, a tomographic image can be obtained with little scattering by blood by filling the portion where optical scanning is performed with physiological saline and setting the state in which blood is excluded. The other effects are almost the same as those of the fourth embodiment.
[0113]
(Eighth embodiment)
Next, an eighth embodiment of the present invention will be described with reference to FIG. FIG. 21 shows the distal end side of an optical scanning probe 8L according to the eighth embodiment of the present invention. This embodiment is provided with a focal position changing means.
[0114]
For example, in the optical scanning probe 8K of FIG. 20, the optical scanning probe 8L does not include the fluid conduit 101, but attaches the distal end of the fourth single mode fiber 9 to the distal end body 44 via the linear actuator 106, and the sheath 42 It can be moved in the longitudinal direction.
[0115]
That is, the tip of the fourth single mode fiber 9 is attached to the rotor (movable part) of the linear actuator 106, and the stator of the linear actuator 106 is attached to the tip body 44. Further, the lead wire 107 connected to the linear actuator 106 is inserted through the sheath 42, and the end on the hand side is connected to a drive circuit (not shown).
[0116]
Then, by operating a focus position variable switch connected to the drive circuit, the rotor side of the niria actuator 106 can be moved forward or backward. For example, in the state of FIG. 21, the focal position F1 is indicated by a one-dot chain line, but when the focal position variable switch is operated to move the tip of the fourth single mode fiber 9 forward to the position indicated by the dotted line, The focal position F2 can be set.
[0117]
According to the present embodiment, since the position of the focusing point of the low interference light emitted from the distal end side of the optical scanning probe 8L can be changed, for example, when obtaining a tomographic image, the depth position obtained in the state with the highest resolution is obtained. Variable setting.
[0118]
More specifically, for example, when a tomographic image is obtained in a normal state in which the operation of changing the focal position is not performed, the focal position is assumed to be F1, and the deeper side is to be observed with higher resolution. In this case, by operating the focal position variable switch to advance the tip of the fourth single mode fiber 9, the focal position can be set to F2 further away, and a tomographic image focused on the deep side can be obtained. .
The other effects are almost the same as those of the fourth embodiment.
[0119]
(Ninth embodiment)
Next, a ninth embodiment of the present invention will be described with reference to FIGS. FIG. 22 shows the distal end side of the optical scanning probe 8M according to the ninth embodiment of the present invention, and FIG.
[0120]
In this embodiment, the single-mode fiber is not rotated, and the light scanning can be performed in the longitudinal direction of the sheath by rotating the reflecting member provided at the tip of the rotating shaft.
[0121]
A single mode fiber 112 is inserted into the cylindrical sheath 111 along a position eccentric from the central axis, and the distal end of the single mode fiber 112 is fixed to the distal end side of the sheath 111 together with the GRIN lens 113 fixed to the distal end surface. It is fixed to the through-hole of the tip member 114 and emits light forward.
[0122]
Further, a flexible rotating shaft 115 is inserted along the central axis of the sheath 111, the distal end side of the rotating shaft 115 passes through the hole of the distal end body 114, and a mirror member 116 is attached to the distal end. 116 is rotated together with the rotating shaft 115.
[0123]
In this mirror member 116, the angle θ of the surface on which the light of the GRIN lens 113 hits changes continuously with the rotation, and when the angle rotates nearly one rotation, it changes discontinuously and again at the end of the surface continuously changing. It is formed to return.
[0124]
Therefore, when the mirror member 116 is rotated at an angle close to approximately one rotation, the optical scanning direction indicated by the two-dot chain line in FIG. 23 includes the optical scanning direction indicated by the one-dot chain line in the middle and the optical scanning direction indicated by the solid line. The optical scanning area 117 can be covered.
This optical scanning region 117 is in the direction included in the paper surface of FIG. Therefore, this embodiment does not perform optical scanning in the circumferential direction, but is along the direction including the axis of the optical scanning probe 8M.
[0125]
This embodiment can also effectively prevent the breakage of the single mode fiber without rotating it. The other effects are almost similar to those of the other embodiments.
[0126]
(Tenth embodiment)
Next, a tenth embodiment of the present invention will be described with reference to FIG. FIG. 24A shows the shape of the light-emitting prism in the tenth embodiment of the present invention.
In FIG. 24A, a microprism 52A is formed by forming a cylinder on the front end surface of the GRIN lens 51 at an angle of 45 ° to form an anti-slope surface. In this case, the light emitted from the tip of the fourth single mode fiber 9 is emitted to the living tissue side as indicated by an arrow through the curved emitting surface of the GRIN lens 51 and the microprism 52A, and is then disposed on the living tissue side. The light reflected by the light follows the reverse optical path and is incident on the distal end side of the fourth single mode fiber 9.
[0127]
FIG. 24B is employed in the first embodiment and the like, and a microprism 52 is formed by cutting a cube on the tip surface of the GRIN lens 51 to form a reflection surface.
[0128]
In addition, in the modification of FIG. 24C, the emission surface in which the cylindrical lens 52C is provided on the light emission surface of the microprism 52 of FIG. 24B is a curved microprism.
In this way, the spot shape at the focused point can be set to a high resolution state in a certain direction by using a curved surface.
[0129]
In FIG. 24A or a modified example of FIG. 24C, the exit surface of the microprism 52A or the cylindrical lens 52C has a curved surface forming a cylindrical shape in the axial direction of the fourth single mode fiber 9. However, a curved cylindrical lens having a cylindrical shape in a direction perpendicular to the axial direction may be attached.
In this way, the cylindrical lens function in the case of transmitting through the sheath is an isotropic lens function by canceling the anisotropic lens function by the cylindrical lens having a cylindrical shape in a direction perpendicular to the cylindrical lens function. You may make it have.
[0130]
Further, for example, instead of the GRIN lens 51 and the microprism 52 in the first embodiment or the second embodiment, the inclined surface which becomes the reflection surface of the microprism 52 is made a convex surface, and the light path is reflected by this convex surface. In addition to the change, a lens function for condensing light (a structure having a lens function for condensing light by the optical path changing means) may be used.
Note that embodiments and the like configured by partially combining the above-described embodiments and the like also belong to the present invention.
[0131]
[Appendix]
1. An optical scanning probe device for an optical imaging apparatus that irradiates a subject with low coherence light and constructs a tomographic image of the subject from information of light scattered in the subject, and is disposed in a forceps channel of an endoscope A thin and flexible cylindrical sheath that can be inserted and the tip is not open, and at least a side surface on the tip side is formed of a light-transmitting material,
A flexible coil shaft rotatably provided around a longitudinal axis inside the sheath;
A rotational drive device for applying a rotational force to the coil shaft;
Light emitted from a low-interference light source is formed of a single mode fiber provided inside the flexible coil shaft, and its base end and tip are fixed to the base end and tip of the coil shaft, respectively. A fiber provided to be incident on its proximal end;
A lens that is provided at a certain distance from the tip of the fiber and that focuses the light emitted from the fiber at a specific position;
Outgoing light path changing means fixed to the lens for changing the optical path of outgoing light;
An optical scanning probe device comprising:
[0132]
2. In Appendix 1,
Lens means for condensing light from the low interference light source is provided at the proximal end of the fiber.
3. In Appendix 2,
In the lens means provided at the base end of the fiber, the effective diameter of the light beam that can enter the fiber is smaller than the diameter of the light beam that enters the lens means.
[0133]
3 '. An optical scanning probe device for an optical imaging apparatus that irradiates a subject with low coherence light and constructs a tomographic image of the subject from information of light scattered in the subject, and is disposed in a forceps channel of an endoscope A thin and flexible cylindrical sheath that can be inserted and the tip is not open, and at least a side surface on the tip side is formed of a light-transmitting material,
A flexible hollow shaft that is rotatably provided around the longitudinal axis inside the sheath;
A rotational drive device for applying a rotational force to the hollow shaft;
It is formed of a single mode fiber provided inside the hollow shaft, and its proximal end and distal end are fixed to the proximal end and distal end of the hollow shaft, respectively, and the light emitted from the low interference light source is A fiber provided to be incident on the proximal end;
An outgoing optical path changing means that is fixed to the distal end of the hollow shaft so as to face the distal end of the fiber, condenses outgoing light emitted from the distal end of the fiber, and changes an optical path of the outgoing light;
An optical scanning probe device comprising:
3 ″. In Supplementary Note 3 ′, the exit optical path changing means has a lens function of condensing light when reflected by a convex reflecting surface of the prism.
[0134]
4). An optical scanning probe device for an optical imaging apparatus that irradiates a subject with low coherence light and constructs a tomographic image of the subject from information of light scattered in the subject,
An elongated and flexible cylindrical sheath that can be inserted into the forceps channel of the endoscope and the tip is not open, and at least a side surface on the tip side is formed of a material having good light transmittance; and
A flexible coil shaft rotatably provided around a longitudinal axis inside the sheath;
A rotational drive device for applying a rotational force to the coil shaft;
A fiber member that is formed of a single mode fiber provided on the rotating shaft of the coil shaft, and is provided so that light emitted from a low interference light source is incident on a base end thereof;
A lens that is fixed to the coil shaft at a specific distance from the tip of the fiber member and condenses the light emitted from the fiber member at a specific position;
Outgoing light path changing means fixed to the lens for changing the optical path of outgoing light;
An optical scanning probe device comprising:
[0135]
5. In Appendix 4,
The fiber member is characterized in that at least a part of the side surface on the distal end side has a large outer diameter, and the diameter is slightly smaller than the inner diameter of the coil shaft.
[0136]
5 '. An optical scanning probe device for an optical imaging apparatus that irradiates a subject with low coherence light and constructs a tomographic image of the subject from information of light scattered in the subject,
An elongated and flexible cylindrical sheath that can be inserted into the forceps channel of the endoscope and the tip is not open, and at least a side surface on the tip side is formed of a material having good light transmittance; and
A flexible coil shaft rotatably provided around a longitudinal axis inside the sheath;
A rotational drive device for applying a rotational force to the coil shaft;
A fiber member that is formed of a single mode fiber provided on the rotating shaft of the coil shaft, and is provided so that light emitted from a low interference light source is incident on a base end thereof;
An outgoing optical path changing means for concentrating the outgoing light emitted from the fiber member and being fixed to the distal end side of the coil shaft so as to face the distal end of the fiber member, and for changing the optical path of the outgoing light,
An optical scanning probe device comprising:
[0137]
6). In Appendix 4,
At least a part of the coil shaft tip side has a small inner diameter, and the diameter is slightly larger than the outer shape of the fiber member.
[0138]
7). An optical scanning probe for an optical imaging apparatus that irradiates a subject with low coherence light and constructs a tomographic image of the subject from information of light scattered in the subject,
An elongated and flexible cylindrical sheath that can be inserted into the forceps channel of the endoscope and the tip is not open, and at least a side surface on the tip side is formed of a material having good light transmittance; and
A flexible shaft rotatably provided around a longitudinal axis inside the sheath;
A rotational drive device for applying a rotational force to the shaft;
A fiber formed of a single mode fiber provided in parallel to the shaft, and provided so that light emitted from a low-interference light source is incident on a base end thereof;
A lens that is fixedly provided on the distal end side of the fiber and collects light emitted from the fiber at a specific position;
A mirror fixed to the tip of the shaft, and an optical path conversion means for converting an optical path of light transmitted through the lens as the shaft rotates;
An optical scanning probe device comprising:
[0139]
8). An optical scanning probe device for an optical imaging apparatus that irradiates a subject with low coherence light and constructs a tomographic image of the subject from information of light scattered in the subject,
An elongated and flexible cylindrical sheath that can be inserted into the forceps channel of the endoscope and the distal end is not open, and is formed of a material having good light transmissivity at least on the side surface on the distal end side;
A fiber that is formed of a single mode fiber provided inside the sheath, and is provided so that light emitted from a low-interference light source is incident on the base end thereof,
A lens that is fixedly provided on the distal end side of the fiber and collects light emitted from the fiber at a specific position;
An ultrasonic motor provided inside the distal end of the sheath;
A power supply and control means for supplying electricity to the ultrasonic motor;
An optical path conversion means fixed to the rotor of the ultrasonic motor, the optical path conversion means converting the optical path of the light transmitted through the lens in accordance with the rotational operation of the ultrasonic motor;
An optical scanning probe device comprising:
[0140]
9. In any one of Supplementary Notes 1, 4, 7, and 8,
The coil shaft or the shaft is made of a super elastic alloy.
10. In any one of Supplementary Notes 1, 4, 7, and 8,
The sheath is characterized by comprising a flexible tube having both ends open and a cap having excellent light transmission provided at the tip of the tube.
[0141]
11. In any one of Supplementary Notes 1, 4, 7, and 8,
The sheath material is polymethylpentene.
12 In any one of Supplementary Notes 1, 4, 7, and 8,
The sheath is characterized by a flexible tube having both ends open, a pipe made of a material having good light transmission connected to the tip of the tube, and a cap sealed at the tip of the pipe.
[0142]
13. In Appendix 12,
The pipe is made of quartz glass.
14 In any one of Supplementary Notes 1, 4, 7, and 8,
At least a part of the sheath includes a member that can be imaged under fluoroscopy.
[0143]
15. In any one of Supplementary Notes 1, 4, 7, and 8,
The optical scanning probe has a pipe line extending in the longitudinal direction, the distal end of the pipe line opens to the side surface of the optical scanning probe, and the proximal end of the pipe line is connected to a pump for supplying fluid. It is characterized by.
16. In any one of Supplementary Notes 1, 4, 7, and 8,
An operation portion capable of bending the optical scanning probe is provided on the proximal end side of the optical scanning probe, and the bending operation portion is located closer to the proximal end than the side surface of the optical scanning probe through which low interference light is transmitted. It is characterized by being.
[0144]
17. In any one of Supplementary Notes 1, 4, 7, and 8,
The optical scanning probe includes an actuator capable of adjusting a distance between a tip surface of the single mode fiber and the lens.
18. In any one of Supplementary Notes 1, 4, 7, and 8,
At least the inner surface on the distal end side of the sheath is filled with a fluid.
[0145]
19. In Appendix 18,
The fluid has a refractive index of about 1.5.
20. In Appendix 18,
The fluid has a refractive index of 1.0 to 2.0.
[0146]
20. In appendix 1, 4, 7, or 8,
The optical path changing means is a prism.
21. In Appendix 20,
The light exit surface of the prism is a curved surface.
[0147]
【The invention's effect】
  As described above, according to the present invention,It is possible to provide an optical scanning probe apparatus that can be inserted into a channel of an endoscope and can obtain a tomographic image by scanning with low interference light.
[Brief description of the drawings]
FIG. 1 is a diagram showing an overall configuration of an optical tomographic imaging apparatus provided with a first embodiment of the present invention.
FIG. 2 is a diagram showing an endoscope through which the first embodiment is inserted.
FIG. 3 is a cross-sectional view showing a rear end side portion of the optical scanning probe device according to the first embodiment of the present invention.
FIG. 4 is a cross-sectional view showing the overall configuration of the optical scanning probe device.
FIG. 5 is a cross-sectional view showing a front end side portion of the optical scanning probe device.
FIG. 6 is a diagram showing a rear end side and the like of a modified example in which a part of the connector portion is changed.
FIG. 7 is a cross-sectional view showing an optical scanning probe device according to a second embodiment of the present invention.
FIG. 8 is a cross-sectional view showing the connector portion in the AA cross section of FIG. 7;
FIG. 9 is a cross-sectional view showing a distal end side of an optical scanning probe device according to a third embodiment of the present invention.
FIG. 10 is a perspective view showing a distal end side of an optical scanning probe device provided with a light shielding mark.
11 is a diagram showing an endoscopic image obtained by imaging the distal end side of the optical scanning probe device of FIG. 10;
12 is a view showing a tomographic image obtained using the optical scanning probe apparatus of FIG.
FIG. 13 is a cross-sectional view showing a distal end side of an optical scanning probe device according to a fourth embodiment of the present invention.
FIG. 14 is a cross-sectional view showing the distal end side of an optical scanning probe device according to a first modification of the fourth embodiment.
FIG. 15 is a cross-sectional view showing the distal end side of an optical scanning probe device according to a second modification of the fourth embodiment.
FIG. 16 is a cross-sectional view showing the distal end side of an optical scanning probe device according to a fifth embodiment of the present invention.
FIG. 17 is a diagram illustrating a state in which a distal end side of an optical scanning probe device according to a fifth embodiment is curved.
FIG. 18 is a sectional view showing the distal end side of an optical scanning probe device according to a sixth embodiment of the present invention.
FIG. 19 is a cross-sectional view showing the distal end side of an optical scanning probe device according to a modification of the sixth embodiment.
FIG. 20 is a cross-sectional view showing the distal end side of an optical scanning probe device according to a seventh embodiment of the present invention.
FIG. 21 is a sectional view showing the distal end side of an optical scanning probe device according to an eighth embodiment of the present invention.
FIG. 22 is a sectional view showing the distal end side of an optical scanning probe device according to a ninth embodiment of the present invention.
FIG. 23 is an operation explanatory diagram of the optical scanning probe device according to the ninth embodiment.
FIG. 24 is a diagram showing the shape of a light-emitting prism in the tenth embodiment of the present invention and its modification.
[Explanation of symbols]
1. Optical tomographic imaging device
2 ... Low coherence light source
3, 5, 7, 9 ... single mode fiber
4 ... Optical coupler
6 ... Rotary joint
8A: Optical scanning probe (device)
11 ... Living tissue
12 ... Photodiode
15: Optical path length variable mechanism
17 ... Mirror
22: Demodulator
25 ... Monitor
27 ... Endoscope
28 ... Forceps insertion port
29 ... Insertion section
31 ... Rotor receiver
32 ... Rotor
37 ... Motor
41 ... Connector
42 ... Sheath
43 ... Connector body
44 ... tip body
45 ... Flexible shaft
46 ... Connector cover
47 ... Bearing
48 ... convex
49 ... concave
51 ... GRIN lens
52 ... Microprism
53 ... outgoing light
54. Antireflection film

Claims (5)

  1. An optical scanning probe device for an optical imaging apparatus that irradiates a subject with low coherence light and constructs a tomographic image of the subject from information of light scattered in the subject,
    Is insertable in an endoscope forceps in the channel, with is formed in the elongated flexible tubular tip is closed, the side surface of at least the tip side of the sheath is molded with good material having optical transparency ,
    Rotatably disposed about a longitudinal axis inside the sheath, and a flexible sheet Yafuto a rotational force Ru is imparted by a rotational driving device,
    And single-mode Fiber provided along the central axis of the sheath to the inside of the flexible sheet Yafuto,
    A lens that is provided on the rear end side of the single mode fiber, and that makes the low coherence light having an effective diameter smaller than the light beam diameter of the incident low coherence light incident on the rear end of the single mode fiber ;
    While being disposed on the distal end side of the single-mode fiber, is rotated by the rotational force is imparted shaft, and the optical path changing means to change the optical path of the light guide light being by the single-mode fiber,
    An optical scanning probe device comprising:
  2. The optical scanning probe apparatus according to claim 1, wherein the single mode fiber rotates together with the shaft by being fixed to a connector provided at a rear end of the shaft.
  3. The optical scanning probe device according to claim 2, wherein the rotation driving device is detachably attached to the connector.
  4. 3. The rotary drive device includes a single mode fiber different from the single mode fiber, and a lens that widens the diameter of emitted light at the tip of the single mode fiber. Or the optical scanning probe apparatus of 3.
  5. The lens fixed to the optical path changing means, provided at a specific distance from the tip of the single mode fiber, and the lens for condensing the light emitted from the single mode fiber at a specific position The optical scanning probe apparatus according to claim 1, further comprising different lenses.
JP23300197A 1997-08-28 1997-08-28 Optical scanning probe device Expired - Fee Related JP4021975B2 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
JP23300197A JP4021975B2 (en) 1997-08-28 1997-08-28 Optical scanning probe device

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
JP23300197A JP4021975B2 (en) 1997-08-28 1997-08-28 Optical scanning probe device
US09/141,430 US6069698A (en) 1997-08-28 1998-08-27 Optical imaging apparatus which radiates a low coherence light beam onto a test object, receives optical information from light scattered by the object, and constructs therefrom a cross-sectional image of the object
US09/141,572 US6327493B1 (en) 1997-08-28 1998-08-27 Light scanning devices of a water-tight structure to be inserted into a body cavity to obtain optical information on inside of a biological tissue

Publications (2)

Publication Number Publication Date
JPH1156786A JPH1156786A (en) 1999-03-02
JP4021975B2 true JP4021975B2 (en) 2007-12-12

Family

ID=16948265

Family Applications (1)

Application Number Title Priority Date Filing Date
JP23300197A Expired - Fee Related JP4021975B2 (en) 1997-08-28 1997-08-28 Optical scanning probe device

Country Status (1)

Country Link
JP (1) JP4021975B2 (en)

Families Citing this family (52)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7180600B2 (en) * 1998-09-21 2007-02-20 Olympus Corporation Optical imaging apparatus
WO2000058766A1 (en) * 1999-03-29 2000-10-05 Scimed Life Systems, Inc. Single mode optical fiber coupling systems
JP2002263055A (en) 2001-03-12 2002-09-17 Olympus Optical Co Ltd Tip hood for endoscope
JP2002263106A (en) 2001-03-12 2002-09-17 Olympus Optical Co Ltd Optical probe device
EP1402244A1 (en) 2001-04-30 2004-03-31 The General Hospital Corporation Method and apparatus for improving image clarity and sensitivity in optical coherence tomography using dynamic feedback to control focal properties and coherence gating
US7251025B2 (en) * 2001-05-17 2007-07-31 Oticon A/S Method and apparatus for obtaining position data relating to a probe in the ear canal
US7206067B2 (en) * 2001-05-17 2007-04-17 Oticon A/S Method and apparatus for obtaining geometrical data relating to the ear canal of the human body
US7365858B2 (en) * 2001-12-18 2008-04-29 Massachusetts Institute Of Technology Systems and methods for phase measurements
JP5416883B2 (en) * 2003-06-19 2014-02-12 マサチユセツツ・インスチチユート・オブ・テクノロジイMassachusetts Institute Of Technology Phase measuring system and method
US6850789B2 (en) * 2002-07-29 2005-02-01 Welch Allyn, Inc. Combination SPO2/temperature measuring apparatus
US6904199B2 (en) * 2002-08-14 2005-06-07 Infraredx, Inc. Optical catheter with double-clad fiber
US20040092829A1 (en) * 2002-11-07 2004-05-13 Simon Furnish Spectroscope with modified field-of-view
US7376455B2 (en) 2003-05-22 2008-05-20 Scimed Life Systems, Inc. Systems and methods for dynamic optical imaging
DE102004011189B4 (en) * 2004-03-04 2011-05-05 Carl Mahr Holding Gmbh Optical measuring head
EP1750569B1 (en) * 2004-03-23 2012-05-09 California Institute Of Technology Forward scanning imaging optical fiber probe
JP5324095B2 (en) * 2004-08-24 2013-10-23 ザ ジェネラル ホスピタル コーポレイション Method and apparatus for imaging blood vessel segments
EP1804638B1 (en) * 2004-09-29 2012-12-19 The General Hospital Corporation System and method for optical coherence imaging
JP4570038B2 (en) * 2005-03-18 2010-10-27 大阪瓦斯株式会社 Dust measuring device
DE102005032961A1 (en) * 2005-07-14 2007-01-18 Siemens Ag Method and device for generating an image by means of optical coherence tomography
JP4804057B2 (en) * 2005-07-28 2011-10-26 オリンパス株式会社 Inner surface measuring device
JP4640813B2 (en) * 2005-09-30 2011-03-02 富士フイルム株式会社 Optical probe and optical tomographic imaging apparatus
JP2007135947A (en) * 2005-11-21 2007-06-07 Fujifilm Corp Optical probe and optical tomographic imaging system
US9087368B2 (en) * 2006-01-19 2015-07-21 The General Hospital Corporation Methods and systems for optical imaging or epithelial luminal organs by beam scanning thereof
WO2008086614A1 (en) * 2007-01-19 2008-07-24 University Health Network Electrostatically driven imaging probe
JP4895840B2 (en) * 2007-01-31 2012-03-14 Hoya株式会社 OCT system
JP5067704B2 (en) * 2007-03-02 2012-11-07 株式会社モリタ東京製作所 Dental OCT device
JP2008289850A (en) * 2007-04-23 2008-12-04 Fujifilm Corp Optical probe and optical tomography apparatus
US7627208B2 (en) 2007-04-23 2009-12-01 Fujifilm Corporation Optical probe and optical tomography apparatus
JP5524835B2 (en) * 2007-07-12 2014-06-18 ヴォルカノ コーポレイションVolcano Corporation In vivo imaging catheter
JP2011519692A (en) * 2008-05-07 2011-07-14 ヴォルカノ コーポレイションVolcano Corporation Optical imaging catheter that cancels aberrations
WO2009049296A2 (en) * 2007-10-12 2009-04-16 The General Hospital Corporation Systems and processes for optical imaging of luminal anatomic structures
DE102007059903A1 (en) * 2007-12-12 2009-06-18 Robert Bosch Gmbh Probe and device for optical testing of test objects
JP5192247B2 (en) * 2008-01-29 2013-05-08 並木精密宝石株式会社 OCT probe
JP5194839B2 (en) * 2008-01-31 2013-05-08 コニカミノルタアドバンストレイヤー株式会社 Rotating light irradiation device
JP2009201969A (en) * 2008-02-01 2009-09-10 Fujifilm Corp Oct optical probe and optical tomography imaging apparatus
JP5241293B2 (en) * 2008-04-01 2013-07-17 富士フイルム株式会社 Optical tomographic image acquisition apparatus and method
JP2010179085A (en) * 2008-07-11 2010-08-19 Canon Inc Biological information acquisition apparatus
JP5521172B2 (en) * 2008-09-22 2014-06-11 公益財団法人ヒューマンサイエンス振興財団 Image printing device
JP5227714B2 (en) * 2008-09-26 2013-07-03 富士フイルム株式会社 Optical probe, optical tomographic imaging device
EP2515150A4 (en) 2009-12-14 2014-04-02 Toyo Seikan Group Holdings Ltd Lateral emission apparatus and manufacturing method thereof
US8380037B2 (en) 2010-03-03 2013-02-19 Toyo Glass Co., Ltd. Lateral light emitting device and method of producing the same
JP5678286B2 (en) * 2010-03-16 2015-02-25 公益財団法人ヒューマンサイエンス振興財団 OCT device for photographing adjacent tooth surface
WO2011114718A1 (en) * 2010-03-16 2011-09-22 財団法人ヒューマンサイエンス振興財団 Dental oct device
JP5696318B2 (en) * 2010-03-16 2015-04-08 公益財団法人ヒューマンサイエンス振興財団 Dental OCT device
WO2013126485A1 (en) * 2012-02-23 2013-08-29 Corning Incorporated Methods of making a stub lense element and assemblies using same for optical coherence tomography applications
US9036966B2 (en) 2012-03-28 2015-05-19 Corning Incorporated Monolithic beam-shaping optical systems and methods for an OCT probe
JP5948168B2 (en) * 2012-07-03 2016-07-06 オリンパス株式会社 Medical manipulator
US20140378846A1 (en) * 2013-06-19 2014-12-25 Canon U.S.A., Inc. Omni-directional viewing apparatus
JP2016202866A (en) * 2015-04-16 2016-12-08 住友電気工業株式会社 The optical probe
JP2016202281A (en) * 2015-04-16 2016-12-08 住友電気工業株式会社 Optical probe
WO2017168628A1 (en) 2016-03-30 2017-10-05 株式会社日立製作所 Three-dimensional-shape measurement device and three-dimensional-shape measurement probe
US20180256032A1 (en) * 2017-03-13 2018-09-13 Go!Foton Holdings, Inc. Optical probe and assembly thereof

Also Published As

Publication number Publication date
JPH1156786A (en) 1999-03-02

Similar Documents

Publication Publication Date Title
Yang et al. Photoacoustic endoscopy
JP4997112B2 (en) Apparatus for transmitting at least one electromagnetic radiation and method of manufacturing the same
US5166787A (en) Endoscope having provision for repositioning a video sensor to a location which does not provide the same cross-sectionally viewed relationship with the distal end
Tearney et al. Scanning single-mode fiber optic catheter–endoscope for optical coherence tomography
US6608684B1 (en) Optical coherent tomography apparatus, fiberoptic lateral scanner and method for studying biological tissues in vivo
US7283247B2 (en) Optical probe system
US6873416B2 (en) Medical scanning system and related method of scanning
EP1526800B1 (en) Scanning miniature optical probes with optical distortion correction and rotational control
US7180600B2 (en) Optical imaging apparatus
JP4471163B2 (en) Optical tomographic image acquisition device
US6809866B2 (en) Optical imaging apparatus
JP5036952B2 (en) Arthroscope that can change the field of view
JP4204577B2 (en) Medical micro-ultrasonic-OCT probe via endoscope
EP1618836A1 (en) Larygoscope with OCT
CN101365375B (en) Method and apparatus for optical imaging via spectral encoding
US7616986B2 (en) Optical fiber scanner for performing multimodal optical imaging
US6527708B1 (en) Endoscope system
CN101686827B (en) Imaging probe with combined ultrasound and optical means of imaging
DE10043162B4 (en) Tube for joining hollow shaft with cam or hub, has shaft end surface aligned with front surface of hub and front surface of head including seal to obtain pressure-resistant sealing connection under application of retention force
US6477403B1 (en) Endoscope system
US7576865B2 (en) Optical coherent tomographic (OCT) imaging apparatus and method using a fiber bundle
JP2008521022A (en) Optical fiber rotator, optical system and method for sample imaging
US20070232893A1 (en) Probe, image diagnostic system and catheter
US20140180133A1 (en) Scanning endoscopic imaging probes and related methods
EP1441215B1 (en) Optical scanning type observation device

Legal Events

Date Code Title Description
A621 Written request for application examination

Free format text: JAPANESE INTERMEDIATE CODE: A621

Effective date: 20040430

A521 Written amendment

Free format text: JAPANESE INTERMEDIATE CODE: A523

Effective date: 20040430

A977 Report on retrieval

Free format text: JAPANESE INTERMEDIATE CODE: A971007

Effective date: 20060607

A131 Notification of reasons for refusal

Free format text: JAPANESE INTERMEDIATE CODE: A131

Effective date: 20070403

A521 Written amendment

Free format text: JAPANESE INTERMEDIATE CODE: A523

Effective date: 20070529

TRDD Decision of grant or rejection written
A01 Written decision to grant a patent or to grant a registration (utility model)

Free format text: JAPANESE INTERMEDIATE CODE: A01

Effective date: 20070925

A61 First payment of annual fees (during grant procedure)

Free format text: JAPANESE INTERMEDIATE CODE: A61

Effective date: 20070928

FPAY Renewal fee payment (event date is renewal date of database)

Free format text: PAYMENT UNTIL: 20101005

Year of fee payment: 3

FPAY Renewal fee payment (event date is renewal date of database)

Free format text: PAYMENT UNTIL: 20101005

Year of fee payment: 3

FPAY Renewal fee payment (event date is renewal date of database)

Free format text: PAYMENT UNTIL: 20101005

Year of fee payment: 3

FPAY Renewal fee payment (event date is renewal date of database)

Free format text: PAYMENT UNTIL: 20111005

Year of fee payment: 4

FPAY Renewal fee payment (event date is renewal date of database)

Free format text: PAYMENT UNTIL: 20111005

Year of fee payment: 4

FPAY Renewal fee payment (event date is renewal date of database)

Free format text: PAYMENT UNTIL: 20121005

Year of fee payment: 5

FPAY Renewal fee payment (event date is renewal date of database)

Free format text: PAYMENT UNTIL: 20131005

Year of fee payment: 6

LAPS Cancellation because of no payment of annual fees