WO2017203707A1 - Système d'endoscope de type à balayage - Google Patents

Système d'endoscope de type à balayage Download PDF

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Publication number
WO2017203707A1
WO2017203707A1 PCT/JP2016/065801 JP2016065801W WO2017203707A1 WO 2017203707 A1 WO2017203707 A1 WO 2017203707A1 JP 2016065801 W JP2016065801 W JP 2016065801W WO 2017203707 A1 WO2017203707 A1 WO 2017203707A1
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WO
WIPO (PCT)
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subject
light
scanning
unit
illumination
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PCT/JP2016/065801
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English (en)
Japanese (ja)
Inventor
遼佑 伊藤
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オリンパス株式会社
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Priority to PCT/JP2016/065801 priority Critical patent/WO2017203707A1/fr
Publication of WO2017203707A1 publication Critical patent/WO2017203707A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor

Definitions

  • the present invention relates to a scanning endoscope system.
  • an optical fiber scanning observation apparatus and method for observing an observation target in a living body by irradiating a subject having light scattering properties such as a living body and measuring backscattered light by irradiating illumination light is known.
  • a subject having light scattering properties such as a living body and measuring backscattered light by irradiating illumination light.
  • Patent Literature 1 to Patent Literature 3 detect return light emitted from a subject and generate an image based on the total light amount, and extract and observe information on changes in the local form of the subject. There is an inconvenience that can not be done.
  • the present invention has been made in view of the above-described circumstances, and an object of the present invention is to provide a scanning endoscope system that can analyze a signal based on a change in the local form of a subject.
  • One embodiment of the present invention includes a light source unit that generates illumination light, an endoscope main body that irradiates a subject with the illumination light emitted from the light source unit, and detects return light from the subject, and the endoscope A variation information extraction unit that extracts time variation information of the subject based on an intensity signal of the return light detected by the mirror body, and the endoscope body includes the illumination light emitted from the light source unit and the An optical fiber that guides return light from the subject, a drive unit that two-dimensionally scans the illumination spot of illumination light by vibrating the tip of the optical fiber, and the tip of the optical fiber
  • a scanning endoscope system comprising: a detection unit that detects return light from the received subject.
  • the illumination light emitted from the light source unit is scanned two-dimensionally in the subject by forming the illumination spot by vibrating the tip of the optical fiber of the endoscope body, and each scanning position in the subject.
  • the return light returning from is received at the tip of the optical fiber and detected by the detector.
  • the variation information extraction unit extracts time variation information of the subject. This makes it possible to observe local changes in the shape of the subject.
  • laser light may be used as the illumination light.
  • low-coherent laser light composed of partially coherent light having a coherence distance that is equal to or larger than the reciprocal of the scattering coefficient of the subject and shorter than half of the reciprocal of the equivalent scattering coefficient may be used as the illumination light. In this way, by irradiating the subject made of scatterers with low coherent light with a short coherence distance, the influence of scattered light reaching the subject deep as noise is reduced, and the return scattered by the surface layer of the subject Interference components based only on light can be acquired.
  • the dynamics for generating the image representing the local dynamics of the subject by associating the temporal variation information of the subject extracted by the variation information extraction unit with the scanning position of the illumination spot.
  • An image generation unit may be provided. In this way, it is possible to visualize and easily observe local changes in the shape of the subject.
  • the diameter dimension of the said illumination spot is smaller than the magnitude
  • the variation information extraction unit takes a local form in which the subject is to be observed from an intensity signal sequence of return light from each scanning position arranged in a direction along the scanning locus of the illumination spot.
  • the intensity signal that fluctuates within the frequency range to which it is based may be extracted.
  • the frequency at which the intensity signal of the return light detected based on the local form of the subject fluctuates is limited to a predetermined frequency range. Therefore, by extracting intensity signals within a predetermined frequency range from all the acquired intensity signal sequences of return light, intensity signals that do not contribute to the local form are excluded, and the local form is more accurately obtained. Changes can be detected.
  • the variation information extracting unit corresponds to the two intensity signal sequences of the return light from the scanning positions arranged in the direction along the scanning locus of the illumination spot acquired at different times.
  • the relative positional relationship between the subject and the endoscope body may change. In such a case, if the analysis is performed in consideration of all the intensity signal sequences, the accuracy is lowered. Therefore, the correlation between the corresponding partial signal sequences constituting the two intensity signal sequences acquired at different times is calculated. The analysis accuracy can be improved by extracting only the intensity signal sequence having a high correlation.
  • the present invention it is possible to analyze the signal based on the change in the local form of the object by reducing the influence of the return light component other than the local form.
  • FIG. 1 is an overall configuration diagram showing a scanning endoscope system according to an embodiment of the present invention. It is a figure which shows the illumination light condensed on a to-be-photographed object by the scanning endoscope system of FIG. It is a figure which shows the relationship between the illumination spot of the illumination light of FIG. 2, and the local form which observes a to-be-photographed object. It is a perspective view which shows an example of the scanning locus
  • FIG. 2 It is a perspective view which shows the concept of the scanning locus
  • FIG. 13 has a correlation. It is a figure which shows the case where the partial signal sequence of FIG. 13 has no correlation. It is a modification of the scanning endoscope system of Drawing 1 which attaches and detaches a dynamic observation unit with an adapter, and is a figure showing a dynamic observation state where a dynamic observation unit was equipped with an adapter.
  • a scanning endoscope system 1 according to an embodiment of the present invention will be described below with reference to the drawings.
  • the scanning endoscope system 1 irradiates the subject O with illumination light from the light source unit 2 and the light source unit 2 and detects return light returning from the subject O.
  • An endoscope main body 3 that performs detection, a fluctuation information extraction unit 4 that extracts temporal fluctuation information of the subject O based on the intensity signal of the return light detected by the endoscope main body 3, and the extracted fluctuation information.
  • An image generation unit 5 that generates an image based on the image generation unit 5 and a display unit 6 that displays an image generated by the image generation unit 5 are provided.
  • the light source unit 2 is a laser light source. More preferably, the laser light source generates low-coherent laser light (low-coherent light) as illumination light.
  • low coherent means that the convex peak of the envelope of the interference component in the spatial intensity pattern generated on the surface of the subject O when the representative point of the subject O is point-irradiated is a unit of irregularities of the fine structure of the subject O. This means that the coherence distance is adjusted so as to be approximately within the size range (within an area of about 90%).
  • the low coherent laser light is more than the reciprocal of the scattering coefficient ⁇ s of the subject O made of a light scatterer and half the reciprocal of the equivalent scattering coefficient ⁇ s ′, as shown in the following equation (1). It means a laser beam having a short coherence distance Lc. 1 / ⁇ s ⁇ Lc ⁇ 1/2 ⁇ s ′ (1)
  • the endoscope body 3 includes a scanning unit 7 that two-dimensionally scans an illumination spot of illumination light emitted from the light source unit 2 on the subject O, and a scanning control unit 8 that controls the scanning unit 7. .
  • the scanning unit 7 includes an optical fiber 9 that guides illumination light, a drive unit 10 that vibrates the tip 9a of the optical fiber 9, and illumination emitted from the tip 9a of the optical fiber 9 that is vibrated by the drive unit 10.
  • a condensing lens 11 that collects light and forms an illumination spot having a predetermined diameter on the subject O is provided.
  • the endoscope body 3 receives light at the distal end 9 a of the optical fiber 9, and detects a return light from the subject O guided through the optical fiber 9 on the proximal end side of the optical fiber 9.
  • the detection part 12 is provided.
  • the demultiplexer / multiplexer 26 guides the illumination light emitted from the light source unit 2 to the tip 9a of the optical fiber 9, and guides the return light from the subject O from the tip 9a of the fiber 9 to the detector 12.
  • the diameter size of the illumination spot is set to be smaller than the local form on the subject O to be observed.
  • the local form is, for example, as shown in FIG. 3, organelles existing in mucosal epithelial layers such as respiratory system (trachea, bronchi, nasal cavity, sinus), fallopian tube, and ventricle.
  • a metachronal wave formed as a group by the whipping motion actively performed by the cilia can be mentioned.
  • the diameter dimension of the illumination spot is set to be smaller than the one-wave interval d of the metachronal wave.
  • the local form is not limited to the ciliary metachronal wave, but means a form that varies in a partial region within the entire scanning range. For example, the movement of red blood cells in the superficial blood vessels and the recovery of the form after partially pressing the subject are also included.
  • the endoscope main body 3 can attach and detach the insertion portion 13 including the scanning unit 7 and the main body unit 14 including the scanning control unit 8 and the detection unit 12 with a connector 15. ing.
  • the drive unit 10 includes, for example, two or more piezoelectric elements (not shown) that bend the optical fiber 9 in two directions orthogonal to the longitudinal direction of the optical fiber 9 and orthogonal to each other.
  • the scanning control unit 8 vibrates at a predetermined frequency to two or more piezoelectric elements constituting the driving unit 10 of the scanning unit 7 in synchronization with the illumination light from the light source unit 2, and sufficiently more than the frequency.
  • a drive signal having an amplitude that increases / decreases in a large cycle is input with different phases.
  • the tip 9a of the optical fiber 9 is vibrated in a spiral shape, and as shown in FIG. 4A, the illumination spot is scanned along the spiral locus on the surface of the subject O.
  • the intensity signal Si of the return light detected by the detection unit 12 by the scanning along the one-time winding scanning locus by the scanning unit 7 is an intensity signal Si that changes in the time axis direction. It is supposed to be acquired as.
  • the variation information extraction unit 4 generates an intensity signal sequence S (p, i) acquired by scanning a plurality of times at different times in the same scanning range of the same subject O. .
  • the generation of the intensity signal sequence S (p, i) initializes the number of scans i (step S1), and acquires the intensity signal Si (p) at the number of scans i and the detection point p (
  • the acquired intensity signal Si (p) is stored in a matrix representing the intensity signal sequence S (p, i) (step S3).
  • the update rate of the multiple scans is performed at a frequency fs that is at least twice as high as the analysis frequency upper limit fc.
  • step S4 It is determined whether or not the number of scans i is equal to or greater than the predetermined number N (step S4). If it is smaller than N, the number of scans i is incremented (step S5), and the processes from step S2 are repeated.
  • the intensity signal sequence S (p, i) is converted into a temporal variation component M (p, i) and non-variation component C (p, i) for each detection point p. (Step S6).
  • MF (p, f) is obtained by frequency analysis of the fluctuation component M (p, i) (step S7).
  • f is a frequency.
  • a frequency component MF (x, y, f) is obtained (step S8).
  • luminance information corresponding to frequency bands f1, f2, and f3 for example, average intensities MFf1 (x, y), MFf2 (x, y), and MFf3 ( x, y) are associated with the numerical values of the respective axes of the image output color system to form an image as follows (step S9).
  • R (x, y) MFf1 (x, y)
  • G (x, y) MFf2 (x, y)
  • B (x, y) MFf3 (x, y)
  • illumination light composed of low-coherent laser light emitted from the light source unit 2 is guided by the optical fiber 9 of the scanning unit 7, and the tip of the optical fiber 9. After being emitted from 9a, the light is condensed by the condensing lens 11, and an illumination spot having a predetermined diameter is formed on the surface of the subject O and irradiated.
  • the illumination light is scattered by the subject O made of a scatterer and emitted from the surface of the subject O in all directions. A part of the illumination light is received by the tip 9 a of the optical fiber 9 emitting the illumination light, and is guided through the optical fiber 9. The light is detected and detected by the detector 12. In this case, since the diameter dimension of the illumination spot is set smaller than the local form of the subject O to be observed, return light reflecting the local form can be generated.
  • the tip 9a of the optical fiber 9 that receives the return light from the subject O is disposed at one central position of the condenser lens 11.
  • the return light emitted from the subject O only the light emitted in one direction is received.
  • the subject O has a fine structure in a local form, only return light emitted in a direction corresponding to the shape of the fine structure at the scanning position is obtained at each scanning position irradiated with the illumination light. It can be detected by receiving light.
  • the direction of the return light emitted from the subject O is different, the return light having a different intensity is detected. Therefore, it is possible to detect the return light returning in a different direction depending on the local form. Therefore, there is an advantage that a local form in the subject O can be observed.
  • the scanning endoscope system 1 by using low-coherent laser light as illumination light, scattered light reaching the deep part of the subject O and scattering scattered at the surface layer portion of the subject O. Interference with light can be reduced, return light can be detected, and return light that well represents the local form of the surface layer of the subject O can be detected. Thereby, there is an advantage that a local form in the subject O can be detected more accurately.
  • the intensity signal of the return light acquired at the same scanning position at different times is converted into temporal variation components M (p, i) and non-variable component C (p, i) are separated, and the fluctuation component M (p, i) is subjected to frequency analysis for each detection point p.
  • the frequency component MF (p, f) is obtained by frequency analysis of the fluctuation component M (p, i), and the frequency component MF (x, y, f) associated with each scanning position is obtained. Since the obtained frequency component MF (x, y, f) is imaged by assigning a color for each frequency band, local variation in the subject O can be visually displayed.
  • the frequency component MF (x, y, f) for each detection point on the scanning trajectory is imaged by assigning a color for each frequency band, but instead of this, FIG. 7A and FIG. As shown in FIG. 7B, the frequency fmax at which the frequency component (x, y, f) at each detection point p becomes the maximum value may be imaged in association with an arbitrary color map (step S10). .
  • the separated non-variable component C (p, i) is also imaged as a non-variable component C (x, y, i) associated with each detection point (step S11), and the frequency component MF (You may decide to display with the image of x, y, f).
  • the appearance of the subject O can be observed from the image of the non-variable component C (x, y.i), and is observed in correspondence with the image of the frequency component MF (x, y, f) displayed together. be able to.
  • the intensity signal at the detection point p instead of the step of generating the intensity signal sequence S (p, i) of the intensity signal Si (p) at the detection point p, the intensity signal at the detection point p.
  • the signal component in the frequency range not related to the local form of the subject O is removed from Si (p), and the intensity signal SCi (p) in the frequency range fm related to the local form is extracted (step S12).
  • the intensity signal sequence SC (p, i) may be generated (step S3 ′). Then, the generated intensity signal sequence SC (p, i) may be separated into a fluctuation component M (p, i) and a non-fluctuation component C (p, i) (step S6 ′).
  • the fluctuation component M (p, i) may be subjected to frequency analysis (step S7), and as shown in FIG. 10, the intensity of the frequency range fm related to the local form without scanning a plurality of times.
  • Luminance information corresponding to the signal SC1 (p) may be associated with each scanning position and presented as a continuous image SC1 (x, y).
  • the frequency range fm related to the local form is that the scanning speed v of the illumination light along the scanning locus, and the pitch of the local form is d1 to d2, v / d1 ⁇ fm ⁇ v / d2 It is.
  • corresponding partial signal sequences Sti (p) and Sti ⁇ corresponding to two intensity signals Si (p) and Si ⁇ 1 (p) detected at adjacent times. 1 (p) is calculated (step S13), it is determined whether or not there is a correlation (step S14), and if the correlation is low, Si (p) is converted to the matrix constituting the intensity signal sequence. It may be excluded from storage. Thereby, there is an advantage that it is possible to prevent a decrease in accuracy due to the intensity signal Sti (p) having a low correlation being used for frequency analysis.
  • the scanning endoscope system 1 including the fluctuation information extraction unit 4 in the main body unit 14 is illustrated, but instead, as shown in FIG. It may be provided as a separate body from the main body 14, and return light may be detected via an adapter 17 that is detachably mounted between the main body 14 and the insertion portion 13, and fluctuation information may be extracted.
  • the dynamic observation unit 16 includes a bandpass filter (BPF) 18 that extracts a wavelength band to be detected, and a light detection unit (detection unit) that detects return light that has passed through the bandpass filter 18. 19 and a fluctuation information extraction unit (dynamic image generation unit) 4 that extracts local fluctuations of the subject O based on the intensity of the return light detected by the light detection unit 19.
  • An output from the fluctuation information extraction unit 4 is supplied to a processing circuit (dynamic image generation unit) 20 of the main body unit 14.
  • the processing circuit 20 includes the scanning control unit 8 and the image generation unit 5 shown in FIG.
  • the light source unit 21 includes laser diodes (LD) 21a, 21b, and 21c for each imaging wavelength (R, G, and B). Illumination light from each of the laser diodes 21 a, 21 b, and 21 c is multiplexed by the RGB multiplexer 22 and guided to the optical fiber 9.
  • LD laser diodes
  • the insertion unit 13 is directly connected to the main body unit 14.
  • a plurality of light receiving optical fibers 23 are arranged around the condensing lens 11, and the return light received by all the optical fibers 23 is spectrally separated by the RGB demultiplexer 24.
  • Detection is performed by light receivers (detectors) 25a, 25b, and 25c for each wavelength (R, G, B), and a normal observation image is generated. Further, in normal observation image generation, the lighting timing of the laser diodes (LD) 21a, 21b, and 21c for each imaging wavelength (R, G, B) is shifted, and a signal detected by one light receiver (detection unit) is detected. You may use the system which image-forms according to the lighting timing for every wavelength.
  • the adapter 17 is inserted between the main body 14 and the insertion portion 13, and the main body 14, adapter 17, and insertion portion are inserted. 13 is connected, and the dynamic observation unit 16 is connected to the optical fiber 9 of the scanning unit 7 provided in the insertion unit 13 via a demultiplexing multiplexer 26 such as a fiber coupler. Accordingly, there is an advantage that normal observation using all the optical fibers 23 and dynamic observation using the return light received via the optical fiber 9 of the scanning unit 7 can be performed simultaneously.
  • the two images When displaying the normal observation image and the dynamic observation image acquired simultaneously in this manner, the two images may be displayed in a superimposed manner. Further, a cursor for designating a position may be displayed on the image, and the frequency at the position where the cursor is displayed may be displayed by a number.
  • the frequency analysis is performed after extracting the local fluctuation component M (p, i) of the subject O.
  • two images acquired at different times are used. The difference between them may be calculated.
  • the standard deviation may be calculated using a plurality of acquired images instead of the frequency.
  • a part of the region may be scanned or a part of the region may be analyzed.

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Abstract

Afin de réduire les effets de composantes de lumière diffusée ambiante et d'analyser des signaux qui sont basés sur des changements de la forme locale d'un objet, la présente invention comprend : une unité de source de lumière (2) qui génère une lumière d'éclairage ; un corps principal d'endoscope (3) qui irradie, sur un objet (O), une lumière d'éclairage qui a été émise depuis l'unité de source de lumière (2) et détecte une lumière de retour provenant de l'objet (O) ; et une unité d'extraction d'informations de variation (4) qui extrait des informations de variation temporelle concernant l'objet (O) sur la base d'un signal d'intensité pour la lumière de retour détectée par le corps principal d'endoscope (3). Le corps principal d'endoscope (3) comprend : une fibre optique (9) qui guide optiquement la lumière d'éclairage émise par l'unité de source de lumière (2) et la lumière de retour provenant de l'objet (O) ; une unité d'entraînement (10) qui amène une pointe (9a) de la fibre optique (9) à osciller et amène ainsi un point qui est éclairé par la lumière d'éclairage à balayer de façon bidimensionnelle l'objet (O) ; et une unité de détection (12) qui détecte la lumière de retour provenant de l'objet (O) qui a été reçue au niveau de la pointe (9a) de la fibre optique (9).
PCT/JP2016/065801 2016-05-27 2016-05-27 Système d'endoscope de type à balayage WO2017203707A1 (fr)

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PCT/JP2016/065801 WO2017203707A1 (fr) 2016-05-27 2016-05-27 Système d'endoscope de type à balayage

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Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH0518717A (ja) * 1991-07-10 1993-01-26 Anritsu Corp 外径測定機
WO2015182198A1 (fr) * 2014-05-28 2015-12-03 オリンパス株式会社 Dispositif d'observation par balayage optique et procédé de fonctionnement de dispositif d'observation par balayage optique

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH0518717A (ja) * 1991-07-10 1993-01-26 Anritsu Corp 外径測定機
WO2015182198A1 (fr) * 2014-05-28 2015-12-03 オリンパス株式会社 Dispositif d'observation par balayage optique et procédé de fonctionnement de dispositif d'observation par balayage optique

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