WO2013035400A1 - Sonde - Google Patents

Sonde Download PDF

Info

Publication number
WO2013035400A1
WO2013035400A1 PCT/JP2012/065305 JP2012065305W WO2013035400A1 WO 2013035400 A1 WO2013035400 A1 WO 2013035400A1 JP 2012065305 W JP2012065305 W JP 2012065305W WO 2013035400 A1 WO2013035400 A1 WO 2013035400A1
Authority
WO
WIPO (PCT)
Prior art keywords
optical
optical fiber
light
fiber system
axis
Prior art date
Application number
PCT/JP2012/065305
Other languages
English (en)
Japanese (ja)
Inventor
祥一 田尾
Original Assignee
コニカミノルタアドバンストレイヤー株式会社
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 コニカミノルタアドバンストレイヤー株式会社 filed Critical コニカミノルタアドバンストレイヤー株式会社
Priority to JP2013532479A priority Critical patent/JP5939255B2/ja
Publication of WO2013035400A1 publication Critical patent/WO2013035400A1/fr

Links

Images

Classifications

    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B23/00—Telescopes, e.g. binoculars; Periscopes; Instruments for viewing the inside of hollow bodies; Viewfinders; Optical aiming or sighting devices
    • G02B23/24—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes
    • G02B23/2407—Optical details
    • G02B23/2461—Illumination
    • G02B23/2469—Illumination using optical fibres
    • 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
    • A61B1/00163—Optical arrangements
    • A61B1/00165—Optical arrangements with light-conductive means, e.g. fibre optics
    • A61B1/00167—Details of optical fibre bundles, e.g. shape or fibre distribution
    • 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
    • A61B1/00163—Optical arrangements
    • A61B1/00186—Optical arrangements with imaging filters
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B23/00—Telescopes, e.g. binoculars; Periscopes; Instruments for viewing the inside of hollow bodies; Viewfinders; Optical aiming or sighting devices
    • G02B23/24—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes
    • G02B23/26—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes using light guides

Definitions

  • the present invention relates to a probe that includes an optical system for irradiating a measurement target region of a living tissue with excitation light and receives the measurement light emitted from the measurement target region, and measures the measurement light.
  • Observation and diagnosis of a body lumen using an electronic endoscope is a diagnostic method that is currently widely used.
  • This diagnostic method has an advantage that the burden on the subject is small because it is not necessary to excise the lesion because the body tissue is directly observed.
  • a method for directly observing a body lumen is considered to be less accurate and accurate than pathological examination after biopsy, and efforts to improve imaging image quality are continuously made.
  • diagnostic devices utilizing various optical principles and ultrasonic diagnostic devices have been proposed, and some of them have been put into practical use. Also in these fields, in order to improve the diagnostic accuracy, a new measurement principle is introduced or a plurality of measurement principles are combined.
  • a fluorescence image endoscope system has also been proposed in which a fluorescence image is acquired and displayed so as to overlap a normal visible image. Such a system is highly promising because it leads to early detection of malignant tumors.
  • a method for determining the state of a tissue by acquiring fluorescence intensity information without forming a fluorescence image. Some of these methods acquire fluorescence without using an image sensor mounted on an electronic endoscope.
  • diagnostic probes for performing such fluorescent diagnosis that is, probes which are in the body via the forceps channel of the endoscope, or which are integrated with the endoscope.
  • fluorescence observation probes described in Patent Documents 1 and 2 they are introduced into the body by being inserted into the forceps channel of the endoscope.
  • Raman spectroscopy can be used as a spectroscopy for obtaining information on tissues in the body using a probe.
  • a feature common to both is that, at the time of measurement, a biological tissue is irradiated with a relatively narrow band of excitation light, and measurement light such as fluorescence and Raman scattered light appearing in a wavelength region different from the excitation light is received.
  • measurement light and excitation light are generally separated using an optical filter.
  • the optical filter is not incorporated in the probe itself but in an attached device, and the measurement light guided by the probe is often optically separated at a later stage of the probe. .
  • the excitation light By transmitting the excitation light through an optical filter installed in front of the exit end of the excitation optical fiber, and blocking the light in the band other than the excitation light including fluorescence and Raman scattered light, Irradiation of the biological tissue with Raman scattered light can be avoided. Also, the excitation light is blocked by an optical filter installed in front of the incident end face of the receiving optical fiber, and light in a band other than the excitation light including fluorescence and Raman scattered light is transmitted, so that a part of the excitation light is transmitted to the receiving optical fiber. Is incident and fluorescence or Raman scattered light is prevented from being generated in the fiber. Only one of such optical filters may be installed as necessary.
  • a plurality of receiving optical fibers are arranged so as to surround the periphery of the excitation optical fiber in a concentric manner. Therefore, the optical filter installed in front of the incident end face of the receiving optical fiber is formed in an annular shape, and the optical filter installed in front of the exit end face of the excitation optical fiber is stored in the hollow portion at the center of the annular shape. It has a small cross-sectional area.
  • the probe described above is easy to manufacture for the purpose of further reducing the diameter from the viewpoint of reducing the burden on the patient and making the probe disposable for the purpose of preventing infection without degrading the measurement performance. Improvement is expected to be required in the future.
  • Patent Document 4 when an optical filter having a different transmission band is composed of a ring-shaped member and a member that fits in the hollow portion, a hole having a small diameter is formed with high accuracy to form the hollow portion.
  • advanced processing technology is required to accurately form a filter that fits in the hollow part, and as the diameter of the probe progresses, it becomes more difficult to process the filter. There is a risk.
  • a part having a high degree of difficulty in processing is used, there is a risk that the ease of manufacturing for disposability cannot be improved.
  • the present invention has been made in view of the above problems in the prior art, and includes an optical system for irradiating a measurement target region of biological tissue with excitation light and receiving measurement light emitted from the measurement target region.
  • An object of the present invention is to provide a probe for measuring the measurement light so that an optical filter having a shape that can be easily formed can be installed. As a result, a probe that is advantageous for reducing the diameter and improving the manufacturability is provided. This is the issue.
  • the invention according to claim 1 for solving the above-described problem includes an optical system for irradiating the measurement target site of the living tissue with the excitation light and receiving the measurement light emitted from the measurement target site.
  • a probe for measuring measurement light As the optical system, A first optical fiber system constituting an excitation light guide for guiding the excitation light; A condensing lens system provided at the tip of the probe, irradiated with the excitation light emitted from the first optical fiber system, and having a positive power for condensing the measurement light; A second optical fiber system constituting a light receiving light guide for receiving and guiding the measurement light collected by the condenser lens system; Interposed in the optical path between the exit end of the first optical fiber system and the condensing lens system, and / or the optical path between the light receiving end of the second optical fiber system and the condensing lens system, With an optical filter that makes the optical transmission characteristics of these two optical paths different, The center of the exit end of the first optical fiber system is installed away from the optical axi
  • a probe for measuring the measurement light by including an optical system for irradiating the measurement target site of the living tissue with excitation light and receiving the measurement light emitted from the measurement target site.
  • a first optical fiber system constituting an excitation light guide for guiding the excitation light
  • a condensing lens system provided at the tip of the probe, irradiated with the excitation light emitted from the first optical fiber system, and having a positive power for condensing the measurement light
  • a second optical fiber system constituting a light receiving light guide for receiving and guiding the measurement light collected by the condenser lens system; Interposed in the optical path between the exit end of the first optical fiber system and the condensing lens system, and / or the optical path between the light receiving end of the second optical fiber system and the condensing lens system, With an optical filter that makes the optical transmission characteristics of these two optical paths different, The center of the exit end of the first optical fiber system is installed away from the optical axi
  • the genus is a topological property and generally refers to the number of holes opened in a curved surface.
  • the term is used as a term for defining the shape of an optical filter. It is used and indicates the number of through holes provided in the flat portion of the optical filter.
  • At least a part of the light receiving end of the second optical fiber system has a longest distance from the output end of the first optical fiber system to the optical axis of the condenser lens.
  • a coordinate system that is smaller than the distance and that passes through the optical axis and the center of the exit end of the first optical fiber system and an optical axis of the condenser lens that is perpendicular to the coordinate axis.
  • the light receiving end face of the second optical fiber system overlaps the intensity center of the focused spot of the measurement light that appears between the optical axis and the output end of the first optical fiber system.
  • the first optical fiber system comprises a plurality of optical fibers bundled individually or a plurality of bundles of optical fibers bundled together in one lump. It is a probe as described in.
  • a virtual boundary line that can divide all optical fibers belonging to the first optical fiber system and all optical fibers belonging to the second optical fiber system into two regions.
  • the invention according to claim 7 is the probe according to claim 6, wherein at least one of the optical filters has a linear outline, and the outline is installed on the virtual boundary straight line.
  • the invention according to claim 8 is the probe according to claim 7, wherein at least one of the optical filters has a rectangular outer shape in a cross section perpendicular to the optical axis.
  • the invention according to claim 9 is the probe according to claim 7, wherein at least one of the optical filters has a D-shaped outer shape in a cross section perpendicular to the optical axis.
  • an optical fiber bundled in a lump that includes an optical fiber belonging to the first optical fiber system, an optical fiber belonging to the second optical fiber system, and a third optical fiber in contact with both optical fibers.
  • an optical filter having a complicated shape having a genus of 1 or more there is no need to apply an optical filter having a shape that is easy to form can be installed. There is an effect that it is possible to promote the improvement of manufacturing efficiency and manufacturing.
  • FIG. 4 is a diagram for explaining the arrangement conditions of optical fibers in the embodiment of the present invention, and is an arrangement diagram in a plane perpendicular to the optical axis O.
  • surface which shows the calculation result of the light reception amount regarding the example shown to FIG. 8A.
  • FIG. 8A It is a top view which shows the optical fiber arrangement
  • surface which shows the calculation result of the light reception amount regarding the example shown to FIG. 9A.
  • FIG. 4 is a plan view showing a filter structure for positioning two optical filters according to the embodiment of the present invention.
  • FIG. 11B is a plan view showing only two optical filters shown in FIG. 11A taken out and separated.
  • the base end of the probe 1 of this embodiment is connected to the base unit 2.
  • the base unit 2 includes a light source for generating excitation light applied to a measurement target site of a living body, a spectroscope for detecting light emitted from the measurement target site as a measurement light by excitation light irradiation, and the like. The detector etc. which become are provided.
  • the endoscope main body 3 is connected to an endoscope processor 4 for controlling each part such as a camera unit and illumination built in the endoscope main body and exchanging data with these respective parts.
  • the endoscope main body 3 includes an insertion portion 3a into the body and an operation portion 3b for performing a bending operation or the like of the insertion portion 3a.
  • the endoscope body 3 is formed with a channel 3c that communicates from an insertion port provided in the operation unit 3b to an opening on the distal end surface of the insertion unit 3a.
  • the probe 1 is inserted into the channel 3c, and as shown in FIG. 2, the tip of the probe 1 is disposed so as to be able to advance and retreat relative to the tip of the endoscope. As shown in FIG.
  • a camera portion 3d composed of an imaging element, an objective lens, etc.
  • a light guide 3e serving as a light emitting portion for endoscope illumination
  • An air / water supply nozzle 3f for injecting a fluid such as a liquid and a tip opening of the channel 3c are provided, and the tip of the probe 1 extends from the channel 3c as necessary.
  • the form of the endoscope described above and the form in which the probe 1 is inserted through the channel 3c of the endoscope are only specific examples for explanation.
  • the form guided into the body of the probe 1 may be a form inserted through the channel 3c of the endoscope or a form inserted alone into the body. Even if the configuration of the probe 1 is integrated with the endoscope main body 3, the present invention can be implemented.
  • the probe 1 includes a first optical fiber system 10, a condensing lens system (condensing lens 11), a second optical fiber system 12, and optical filters 13 and 14 inside the probe tube 9. And a ferrule 15.
  • the first optical fiber system 10 is provided so that the base end is connected to or close to the excitation light output surface of the light source of the base unit 2, and the tip extends to the probe tip as shown in FIG.
  • An excitation light guide for guiding light is configured.
  • the condensing lens system is a lens or a lens group having a positive power that collects the measurement light emitted from the measurement target region and irradiated with the excitation light emitted from the first optical fiber system 10.
  • the second optical fiber system 12 has a proximal end connected to the input end to the detector of the base unit 2 and a distal end extending to the probe distal end as shown in FIG. A light receiving light guide path that receives and guides light is configured.
  • the first and second optical fiber systems 10 and 12 are configured by a bundle or a plurality of bundles of optical fiber bundles (fiber bundles) bundled together, or by one or a plurality of individual optical fibers that are not bundled together. Various forms can be applied, including combinations and combinations thereof.
  • the first and second optical fiber systems 10 and 12 are held at predetermined relative positions by the ferrule 15.
  • the condensing lens system is composed of one or a plurality of lenses. In the case of one, it is the condensing lens 11, and when it is composed of a plurality of lenses, the optical fiber systems 10, 12 are the most.
  • a lens arranged at a close position is referred to as a condenser lens 11.
  • FIG. 3 only one condenser lens 11 is illustrated, but another lens constituting the condenser lens system may be disposed on the opposite side of the condenser lens 11 with respect to the optical fiber systems 10 and 12.
  • the distal end of the first optical fiber system 10 facing the condenser lens 11 is the emitting end
  • the distal end of the second optical fiber system 12 facing the condenser lens 11 is the light receiving end.
  • Excitation light from the light source of the base unit 2 is guided to the tip of the probe 1 by the first optical fiber system 10.
  • the excitation light emitted from the emission end of the first optical fiber system 10 is collected by the condenser lens system, emitted from the probe 1, and irradiated onto the measurement target site on the surface of the living tissue. Fluorescence is generated according to the lesion state by the excitation light irradiated to the measurement target site.
  • the measurement light from the measurement target site including the generated fluorescence and the reflected light on the surface of the living tissue is incident on the probe 1, collected by the condenser lens system, and incident on the light receiving end of the second optical fiber system 12. Further, the measurement light is guided by the second optical fiber system 12.
  • the measurement light guided by the second optical fiber system 12 is input to the detector of the base unit 2.
  • Fluorescence is broadly defined as an object irradiated with X-rays, ultraviolet rays, or visible light absorbs its energy, excites electrons, and releases excess energy as electromagnetic waves when it returns to the ground state. To do.
  • fluorescence having a wavelength different from the wavelength is generated as the return light by the excitation light, it is received as measurement light and guided to the detector of the base unit 2 via the second optical fiber system 12.
  • the lesion state to be measured is detected. Instead of measuring fluorescence, Raman scattered light generated due to excitation light may be received and measured.
  • the optical filter 13 is an excitation light transmission filter that transmits excitation light and blocks light in a band other than the excitation light.
  • the optical filter 13 is interposed in the optical path between the emission end of the first optical fiber system 10 and the condenser lens 11. Light emitted from the emission end of the first optical fiber system 10 enters the optical filter 13. Therefore, the fluorescence and Raman scattered light generated in the first optical fiber system 10 can be converted into the living body by transmitting the excitation light through the optical filter 13 and blocking light in a band other than the excitation light including fluorescence and Raman scattered light. Irradiation of the tissue can be avoided.
  • the optical filter 14 is an excitation light blocking filter that blocks excitation light and transmits light in a band other than the excitation light.
  • the optical filter 14 is interposed in the optical path between the condenser lens 11 and the light receiving end of the second optical fiber system 12. The light that has passed through the optical filter 14 enters the light receiving end of the second optical fiber system 12. Accordingly, the excitation light is blocked by the optical filter 14, and light including fluorescence and Raman scattered light in a band other than the excitation light is transmitted, so that part of the excitation light is incident on the second optical fiber system 12 and the second light is transmitted. It is possible to avoid generation of fluorescence or Raman scattered light in the optical fiber system 12.
  • the optical filters 13, 14 for example, a part of one side of the optical filters 13, 14 is bonded to the end surface of the ferrule 15, or the outer peripheral edges of the optical filters 13, 14 are bonded to the inner surface of the probe tube 9. Can be fixed. Further, the optical filters 13 and 14 and further the condenser lens 11 may be held and fixed by applying a holding component connected and fixed to the ferrule.
  • the purpose of the optical filter is not limited to what has been described above or to any purpose.
  • an optical filter having a shape that can be easily formed can be installed by adopting the configuration described later.
  • the center of the emission end of the first optical fiber system 10 is installed away from the optical axis of the condensing lens 11 in order to enable installation of an optical filter having a shape that is easy to form. (Condition a).
  • the central axis of the emission end of the first optical fiber system 10 and the central axis of the light receiving end of the second optical fiber system 12 are parallel to the optical axis of the condenser lens 11.
  • Calculation Example 1 the distribution of reflected light when light is emitted from one optical fiber having a core diameter corresponding to the first optical fiber system 10 of 0.10 [mm] and a numerical aperture (NA) of 0.22. Is calculated. Assume an optical system including a condenser lens L as shown in FIG.
  • a surface perpendicular to the optical axis of the condenser lens L is assumed on both sides of the condenser lens L.
  • One is a surface A arranged on the S1 surface side.
  • the output end of the optical fiber is assumed to be included in the surface A.
  • the other is a surface B arranged on the S2 surface side.
  • the surface B is assumed as the surface of a living tissue and is a surface having complete diffuse reflection.
  • the distribution of light reaching the surface A from the surface B through the condenser lens L is set as a calculation target.
  • the distance between the surface A and the S1 surface is set to 1.37 [mm]
  • the distance between the surface B and the S2 surface is set to 1.7 [mm].
  • FIGS. 5A and 5B depict the reflected light distribution on the surface A based on the calculation results.
  • the intersection of the ordinate and the abscissa corresponds to the position of the optical axis
  • the “x” mark is the center position of the emission end of the optical fiber.
  • the optical axis coincides with the center of the exit end of the optical fiber.
  • the optical axis is separated from the center of the exit end of the optical fiber. This is for examining the case where the center of the emission end of the first optical fiber system 10 is installed away from the optical axis of the condenser lens 11 in accordance with the condition a described above.
  • excitation light is assumed as light to be calculated. In practice, it is important to take fluorescence or Raman scattered light into the second optical fiber system 12 as measurement light. However, since the distribution of the fluorescence and Raman scattered light on the surface A shows the same tendency as the distribution of the reflected light on the surface A when the excitation light is reflected on the surface B, the calculation is made only with the excitation light.
  • the reflected light distribution R1 is also distributed around the optical axis.
  • the center of the reflected light distribution R2 is the optical axis. It can be seen that the optical fiber moves in the direction of the center of the optical fiber (marked with “ ⁇ ”). When the center of the optical fiber (“x” mark) is used as a reference, the center of the reflected light distribution R2 is unevenly distributed on the optical axis side.
  • the center of the reflected light distribution R2 is closer to the center of the optical fiber (marked with “ ⁇ ”) with respect to the optical axis, and closer to the optical axis with respect to the center of the optical fiber (marked with “x”). It is located between the center ("x" mark).
  • the optical paths L1 and L2 shown in FIG. 4 indicate the optical paths from the surface A to the surface B when the optical axis is separated from the center of the output end of the optical fiber.
  • Example 1-1 where the center of the optical fiber that emits the excitation light is on the optical axis of the lens (FIG. 5A), the measurement light is circularly symmetric about the center of the optical fiber that emits the excitation light and the optical axis of the lens. Distributed. Therefore, in order to receive more measurement light, for example, as shown in FIG. 6A, the second optical fiber system 12 that receives the measurement light is surrounded by the first optical fiber system 10 that emits the excitation light. It must be arranged in a ring. Therefore, as an optical filter for blocking unnecessary light generated in the first optical fiber system 10 and an optical filter for blocking excitation light incident on the second optical fiber system 20, an annular member and its The necessity to comprise with the member which fits in a hollow part arises.
  • Example 1-2 in which the optical fiber that emits the excitation light is at a position off the optical axis of the lens (FIG. 5B), the distribution center of the measurement light is relative to the center of the optical fiber that emits the excitation light. It is unevenly distributed on the lens optical axis side. Therefore, when the first optical fiber system 10 that emits the excitation light is shifted from the optical axis of the lens, there is no need to install the second optical fiber system 12 so as to surround the first optical fiber system 10, for example, FIG. As shown in FIG. 6B to FIG. 6I, the second optical fiber system 12 that receives the measurement light may be installed only in the region where the measurement light is mainly distributed.
  • At least a part of the light receiving end of the second optical fiber system 12 has a distance from the output end of the first optical fiber system 10 to the optical axis of the condensing lens 11. (Ie, the distance between the optical axis of the condensing lens L and the portion farthest from the optical axis of the condensing lens L) at the exit end of the first optical fiber system 10. .
  • the distribution center of the measurement light is closer to the optical axis side of the condenser lens 11 with respect to the first optical fiber system 10.
  • the region farther from the first optical fiber system 10 than the first optical fiber system 10 is This is because it is not preferable as an installation area of the second optical fiber system 12. Therefore, “all of the light receiving ends of the second optical fiber system 12 are arranged such that the distance to the optical axis of the condenser lens 11 is smaller than the longest distance from the emitting end of the first optical fiber system 10 to the condenser lens. It is preferable that the condition is “Conditional 1-1”. The configuration illustrated in FIGS. 6B to 6I satisfies this condition 1-1.
  • At least a part of the light receiving end of the second optical fiber system 12 is light that is perpendicular to the coordinate axis passing through the optical axis of the condensing lens 11 and the center of the output end of the first optical fiber system 10.
  • the optical system is arranged in a coordinate area closer to the first optical fiber system 10 than the optical axis.
  • the distribution center of the measurement light is closer to the center of the exit end of the first optical fiber system 10 with respect to the optical axis of the condenser lens 11.
  • the coordinate area closer to the first optical fiber system 10 than the optical axis is the second optical fiber system 12. Suitable as an installation area. For this reason, condition 2 is specified.
  • FIG. 7A is a perspective view depicting the optical axis O of the condenser lens and the first optical fiber system 10.
  • An arrangement example of the emission end of the first optical fiber system 10 and the light reception end of the second optical fiber system 12 on a plane perpendicular to the optical axis O is shown in FIG. 7B.
  • a circle C is a circle centered on the optical axis O and in contact with the first optical fiber system 10 on the inside.
  • the condition 1-1 can be rephrased as placing the second optical fiber system 12 in the circle C.
  • the optical fiber system 12 will not protrude beyond the first optical fiber system 10, and the installation space will be larger than the optical fiber system 10 can be accommodated. Can be suppressed. Further, if the second optical fiber system 12 is installed in the circle C, the distance from the light receiving end of the optical fiber system 12 to the optical axis O is less than that of the output end of the first optical fiber system 10. 1 is satisfied.
  • the coordinates XY are orthogonal biaxial coordinates with the optical axis O as the origin.
  • the coordinate axis X passes through the optical axis O and the center of the emission end of the first optical fiber system 10.
  • a positive region of X with the coordinate axis Y as a boundary is defined as X1, and a negative region is defined as X2.
  • the exit end of the optical fiber system 10 exists in the positive region X1.
  • Condition 2 can be rephrased as “at least a part of the light receiving end of the second optical fiber system 12 is in the positive region X1”. This is because the distribution of the measurement light is mainly distributed in the positive region X1 as confirmed in the calculation example 1 even within the circle C according to the condition 1-1.
  • condition 1-1 and the condition 2 are satisfied as a minimum requirement.
  • the configuration illustrated in FIGS. 6B to 6I satisfies condition a, condition 1-1, and condition 2.
  • the central axis of the cylinder drawn with a two-dot chain line corresponds to the lens optical axis.
  • the light receiving ends 12a and 12b of the second optical fiber system 12 shown in FIG. 7B satisfy the conditions 1-1 and 2.
  • the light receiving end 12a is entirely within the circle C and in the positive region X1
  • the light receiving end 12b is entirely within the circle C and a part thereof is in the positive region X1.
  • FIGS. 6B, 6H, 6D, and 6C are compared with the arrangement examples shown in FIGS. 6A, 6E, 6F, 6G, and 6I.
  • the number of optical fibers is small, which is advantageous for reducing the diameter and improving the ease of manufacture.
  • FIG. 6B has the smallest number of optical fibers and is most advantageous for reducing the diameter and improving the ease of manufacture.
  • FIGS. 6I, 6G, and 6F has a large number of light receiving optical fibers and a large light receiving area. Therefore, the other optical fibers shown in FIGS. 6A, 6B, 6C, 6D, 6E, and 6H are used. Compared to the arrangement example shown, it is advantageous for capturing the measurement light more reliably. Furthermore, since the optical fiber arrangement shown in FIGS. 6E, 6G, and 6H has a large number of optical fibers for irradiating excitation light and a large area of the exit surface, the other optical fibers shown in FIGS. 6A, 6B, 6C, 6D, and 6 Compared to the arrangement example shown in FIG. 6F and FIG. 6I, it is advantageous in reducing the number of optical fibers for light reception and the area of the light receiving end.
  • the second optical fiber system 12 is centered on the intensity center of the condensed spot of the measurement light appearing between the optical axis O and the exit end of the first optical fiber system 10. It is effective that it is installed so that the light receiving ends of each other overlap.
  • the intensity center of the condensing spot of the measurement light is the point where the light intensity of the measurement light is the highest. Making the intensity center of the condensing spot of the measurement light appear between the optical axis O and the exit end of the first optical fiber system 10 (excluding the region overlapping the exit end) is an optical of the condensing lens system.
  • calculation example 2 is disclosed.
  • the light receiving end of the optical fiber is arranged concentrically with Example 2-1 and the optical axis of the condenser lens is shifted from the output end center of the optical fiber so that the light receiving end of the optical fiber is aligned with the reflected light distribution.
  • the light receiving efficiency of Example 2-2 arranged is compared by calculation.
  • the excitation light is emitted by one optical fiber and received by six optical fibers.
  • the core diameter of the optical fiber that emits the excitation light is 0.20 [mm]
  • the numerical aperture (NA) is 0.22
  • the core diameter of each optical fiber that receives light is 0.20 [mm]
  • the numerical aperture (NA) is 0.2.
  • a surface perpendicular to the optical axis of the condenser lens L is assumed on both sides of the condenser lens L. One is a surface A arranged on the S1 surface side.
  • Example 2-1 the optical fiber arrangement shown in FIG. 8A is taken, and in Example 2-1, the optical fiber arrangement shown in FIG. 9A is taken.
  • the white circles numbered 1 to 6 shown in FIG. 8A are the light receiving ends of the optical fibers that receive light.
  • the white line circle adjacent to the light receiving end number 1 is the outer shape of the exit end of the optical fiber that emits the excitation light.
  • the distance between the center of the exit end of the optical fiber that emits the excitation light and the optical axis of the condenser lens L is 0.25 [mm].
  • the distance between the center of the exit end of the optical fiber that emits the excitation light and the optical axis of the condensing lens L is 0 [mm]
  • the circumference of the optical fiber that emits the excitation light as shown in FIG. 9A 6 optical fibers for receiving light were arranged.
  • Example 2-2 the amount of light received by each optical fiber when the amount of excitation light is 1 and the total amount are shown in a table form in FIG. 8B.
  • Example 2-1 the total amount of light received by each optical fiber when the amount of excitation light is 1 is shown in FIG. 9B.
  • Example 2-1 the amount of light received by each optical fiber is equal.
  • Example 2-2 when the number of optical fibers to be received is the same, even if the arrangement of Example 2-2 is adopted, light reception efficiency equal to or higher than that of Example 2-1 should be achieved.
  • the number of optical fibers that receive light is reduced.
  • the reduction in the amount of received light can be made smaller than the concentric arrangement of Example 2-1. That is, in Example 2-1, for example, if the number of optical fibers to be received is reduced by 3, the amount of received light is necessarily halved.
  • the amount of received light is larger than half. If the number of optical fibers is 1, the number of received optical fibers is 1, and the number of optical fibers of numbers 1, 2, 3, 5, and 6 is left.
  • the center of the emission end of the first optical fiber system 10 is set away from the optical axis of the condensing lens 11, so that the same light reception can be achieved without arranging the optical fiber to receive light in an annular shape. Efficiency can be achieved. For this purpose, the above condition 1, and further, conditions 1-1, 2 and 3 are effective.
  • condition 4 it is preferable to satisfy the following condition 4 in order to separate the installation area of the optical filter by a straight line, and thus to install an optical filter having a shape that is easy to form. That is, as condition 4, “a virtual boundary straight line (straight line D in FIG. 7B) that can divide all optical fibers belonging to the first optical fiber system and all optical fibers belonging to the second optical fiber system into two regions can be set. The condition is that these optical fibers are installed.
  • the boundary straight line D may or may not be orthogonal to the coordinate axis X.
  • the boundary straight line D is drawn perpendicularly to the coordinate axis X, but it is also possible to draw it so as to intersect with the coordinate axis X obliquely. It is sufficient that at least one boundary straight line D can be set, but if a plurality of boundary straight lines D can be set, the shape of the optical filter and the degree of freedom of installation are further increased.
  • the center of the reflected light distribution on the surface A is located between the optical axis of the condenser lens and the exit end of the optical fiber, as described with reference to FIGS. 5A and 5B. Therefore, it becomes possible to separate the light receiving end of the optical fiber from the output end of the optical fiber with a certain straight line as a boundary.
  • the optical filter 14 since the second optical fiber system 12 is not arranged in an annular shape around the first optical fiber system 10 by satisfying the above-described condition 1-1, the optical filter 14 needs to be formed in an annular shape. It can be formed in a simple shape with the genus 0 together with the optical filter 13. Thereby, processing of an optical filter becomes easy. Furthermore, if the condition 4 is satisfied, the optical filter 13 and the optical filter 14 can be separated and arranged by the boundary straight line D, and it is necessary to form a complicated outer shape in the vicinity of the boundary in the optical filters 13 and 14. Disappear. This further facilitates the processing of the optical filter.
  • FIG. 10A to FIG. 10G show configuration examples of the shape and arrangement of the optical filter on the plane perpendicular to the optical axis.
  • the configuration shown in FIGS. 10A to 10G satisfies the conditions 1-1 and 4.
  • 10A to 10G show various forms and arrangements, but the reference numerals are the same as those in FIG. 3 for simplicity.
  • the outer shape of the optical filter 13 and the optical filter 14 shown in FIGS. 10A and 10C and the outer shape of the optical filter 14 shown in FIG. 10D are rectangular. If it is a rectangle, each side only needs to be processed into a linear shape, so that it can be easily processed with high accuracy by dicing or the like. Further, a straight side can be arranged on the boundary straight line D.
  • the outer shape of the optical filter 13 and the optical filter 14 shown in FIG. 10B and the outer shape of the optical filter 13 shown in FIG. 10D are circular.
  • the outer shapes of the optical filter 13 and the optical filter 14 shown in FIGS. 10E, 10F, and 10G are D-shaped. If it is D-shaped, its one side can be processed into a straight line shape with high accuracy, and one straight side can be arranged on the boundary straight line D.
  • FIG. 10A, FIG. 10C, FIG. 10D, FIG. 10E, FIG. 10F, and FIG. 10G when the optical filters 13 and 14 have straight outlines, the outlines are the virtual boundary straight lines D described above. Installed on top.
  • the first optical fiber system 10 is a plurality of optical fibers or a plurality of optical fiber bundles in which each bundle is bundled. Is also easy.
  • the optical filter is composed of an annular member and a member that can be accommodated in the hollow part in the conventional technology described above, the excitation light is emitted depending on the inner diameter of the hollow part and the outer diameter of the member that is accommodated in the hollow part. It is necessary to process with high accuracy according to the outer diameter of the optical fiber.
  • an optical filter having a size larger than the end face profile of the corresponding optical fiber can be applied, and even when the corresponding optical fiber is composed of a plurality of optical fibers, their arrangement is also possible.
  • Optical filters with dimensions larger than the area can be applied. Therefore, since a relatively large shape is processed, the ease of processing increases.
  • An optical fiber bundle (fiber bundle) 20 shown in FIG. 10G is bundled into a plurality of optical fibers belonging to the first optical fiber system 10, a plurality of optical fibers belonging to the second optical fiber system 12, and optical fibers of both systems. And third optical fibers 16 and 16 in contact with each other. And the optical fiber installed on the virtual boundary straight line D mentioned above is made into the 3rd optical fiber 16 and 16, and the separability by the linear boundary of the 1st optical fiber system 10 and the 2nd optical fiber system 12 is provided. Can be secured. Moreover, by using the fiber bundle 20, the complexity of positioning and fixing each of the fibers is eliminated, and the ease of assembly is improved.
  • the third optical fiber 16 does not belong to the first optical fiber system 10 or the second optical fiber system 12, that is, it is not used for guiding excitation light or receiving measurement light.
  • the third optical fiber 16 may be used as an optical element for other purposes.
  • the third optical fiber 16 is configured in the base unit 2 even if the probe 1 is connected to the base unit 2. Configure to remain disconnected from the system.
  • the base 1 of the third optical fiber 16 is separated from the first optical fiber system 10 and the second optical fiber system 12 and is held at a location separated from the connector at the base end of the probe 1 to configure the probe 1. To do.
  • the optical filters 13 and 14 are produced by processing a filter material produced by vapor deposition or sputtering on a substrate into a desired shape. This is fixed at a predetermined position with respect to the optical fiber by bonding or the like as described above. Further, it is produced by directly depositing materials constituting the optical filters 13 and 14 on the end faces of the first and second optical fiber systems 10 and 12 by vapor deposition or sputtering.
  • the material which comprises an optical filter is formed in the integral layer form ranging over the end surface of several optical fibers, or the end surface of a ferrule. At this time, in the step of forming the optical filter 13, the end face of the second optical fiber system 12 is masked.
  • the end face of the first optical fiber system 10 is masked.
  • the processability according to the shape and size of the optical filter described above is directly reflected in the ease of forming the masking member, and as a result, the ease of forming the optical filter is achieved. .
  • the optical filters 13 and 14 can also be provided with the shape which mutually positions each other.
  • a concave shape is provided in one optical filter
  • a convex shape is provided in the other optical filter.
  • the structure With such a structure, handling of a fine optical filter is facilitated, and the ease of assembly of the probe 1 is improved.
  • the emission end of the excitation light guiding optical fiber and the light receiving end of the measurement light receiving optical fiber are described as being in the same plane. There is no.
  • the positions where both can be regarded as being in the same plane or substantially in the same plane. It is preferable to arrange in.
  • the present invention can be used for optical measurement of living tissue.
  • Probe tube 10 1st optical fiber system (excitation light emission system) 11 Condenser lens 12 Second optical fiber system (measurement light receiving system) 13, 14 Optical filter 15 Ferrule 16 Third optical fiber D Boundary straight line O Optical axis R1 Reflected light distribution R2 Reflected light distribution

Abstract

En vue de permettre l'installation d'un filtre optique avec une forme qui peut être facilement formée, une sonde selon l'invention pour l'irradiation d'un site à mesurer dans un tissu biologique avec de la lumière d'excitation et pour la réception de la mesure de la lumière irradiant du site à mesurer inclut : un premier système de fibre optique (10) qui guide la lumière d'excitation; un système de lentille collectrice (11) avec une puissance positive pour la collecte de la lumière de mesure; un second système de fibre optique (12) qui reçoit la lumière de mesure collectée au moyen du système de lentille collectrice; et des filtres optiques (13, 14) disposés dans un chemin optique entre une extrémité de sortie du premier système de fibre optique et le système de lentille collectrice ou/et entre le système de lentille collectrice et une extrémité recevant la lumière du second système de fibre optique. Le centre de l'extrémité de sortie est déplacé à partir d'un axe optique de la lentille. La distance entre au moins une partie de l'extrémité recevant la lumière et l'axe optique de la lentille est plus petite que la distance maximum entre l'extrémité de sortie et l'axe optique de la lentille. L'au moins une partie de l'extrémité recevant de la lumière est disposée dans une aire de coordination plus proche du premier système de fibre optique que de l'axe optique de la lentille dans un système de coordination représenté par un axe de coordination passant par l'axe optique de la lentille et le centre de l'extrémité de sortie et un axe optique de lentille perpendiculaire à l'axe de coordination.
PCT/JP2012/065305 2011-09-09 2012-06-15 Sonde WO2013035400A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
JP2013532479A JP5939255B2 (ja) 2011-09-09 2012-06-15 プローブ

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2011-197172 2011-09-09
JP2011197172 2011-09-09

Publications (1)

Publication Number Publication Date
WO2013035400A1 true WO2013035400A1 (fr) 2013-03-14

Family

ID=47831860

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2012/065305 WO2013035400A1 (fr) 2011-09-09 2012-06-15 Sonde

Country Status (2)

Country Link
JP (1) JP5939255B2 (fr)
WO (1) WO2013035400A1 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2019049537A (ja) * 2017-08-30 2019-03-28 三星電子株式会社Ｓａｍｓｕｎｇ Ｅｌｅｃｔｒｏｎｉｃｓ Ｃｏ．，Ｌｔｄ． 分光器用集光光学系、及びそれを含むラマン分光システム

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR101905975B1 (ko) * 2016-09-13 2018-10-10 한국광기술원 플라즈몬 라만 프로브 및 이를 이용한 내시경 장치

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2002136469A (ja) * 2000-10-31 2002-05-14 Machida Endscope Co Ltd 血管内壁の付着物質の分析システム
JP2006317319A (ja) * 2005-05-13 2006-11-24 Institute Of Physical & Chemical Research 血管診断用分光プローブ
JP2007536974A (ja) * 2004-05-14 2007-12-20 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ 光ファイバプローブ
JP2008506426A (ja) * 2004-07-02 2008-03-06 ザ ジェネラル ホスピタル コーポレイション ダブルクラッドファイバを有する内視鏡撮像プローブ
JP2010158358A (ja) * 2009-01-07 2010-07-22 Furukawa Electric Co Ltd:The バンドルファイバ及び内視鏡システム

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2006317329A (ja) * 2005-05-13 2006-11-24 Sadayori Hoshina 輸血製剤中の溶存酸素濃度消費曲線の傾きを指標とした輸血製剤の微生物汚染の検出方法

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2002136469A (ja) * 2000-10-31 2002-05-14 Machida Endscope Co Ltd 血管内壁の付着物質の分析システム
JP2007536974A (ja) * 2004-05-14 2007-12-20 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ 光ファイバプローブ
JP2008506426A (ja) * 2004-07-02 2008-03-06 ザ ジェネラル ホスピタル コーポレイション ダブルクラッドファイバを有する内視鏡撮像プローブ
JP2006317319A (ja) * 2005-05-13 2006-11-24 Institute Of Physical & Chemical Research 血管診断用分光プローブ
JP2010158358A (ja) * 2009-01-07 2010-07-22 Furukawa Electric Co Ltd:The バンドルファイバ及び内視鏡システム

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2019049537A (ja) * 2017-08-30 2019-03-28 三星電子株式会社Ｓａｍｓｕｎｇ Ｅｌｅｃｔｒｏｎｉｃｓ Ｃｏ．，Ｌｔｄ． 分光器用集光光学系、及びそれを含むラマン分光システム
JP7253885B2 (ja) 2017-08-30 2023-04-07 三星電子株式会社 分光器用集光光学系、及びそれを含むラマン分光システム

Also Published As

Publication number Publication date
JPWO2013035400A1 (ja) 2015-03-23
JP5939255B2 (ja) 2016-06-22

Similar Documents

Publication Publication Date Title
US8219180B2 (en) System and method employing fiber optic shape tracking
WO2013061590A1 (fr) Sonde optique et procédé de fabrication de celle-ci
US9820653B2 (en) Methods, systems, and devices for imaging microscopic tumors
JP5400397B2 (ja) バンドルファイバ及び内視鏡システム
US8700135B2 (en) Optical fiber array probe imaging system integrated with endoscope
JP6389828B2 (ja) 医用撮像装置と共に使用するための光学装置
JP5939255B2 (ja) プローブ
US8201997B1 (en) Imaging temperature sensing system
JP5831456B2 (ja) プローブ
JP2013223635A (ja) プローブ
JP5831543B2 (ja) プローブ
JP5864105B2 (ja) 光プローブ
JP5733163B2 (ja) プローブの製造方法
JP5776501B2 (ja) プローブシステム
JP5413204B2 (ja) プローブ
JP6240391B2 (ja) 腹腔鏡
US20230134454A1 (en) Sealed imaging devices
KR101911352B1 (ko) 다중 형광 검출 장치
WO2011083836A1 (fr) Sonde
JP2023079018A (ja) 生体情報収集プローブ
JP5650551B2 (ja) ファイバスコープ装置
KR20060102899A (ko) 광학용 집광유닛 및 그를 포함한 건강 진단기

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 12830454

Country of ref document: EP

Kind code of ref document: A1

ENP Entry into the national phase

Ref document number: 2013532479

Country of ref document: JP

Kind code of ref document: A

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 12830454

Country of ref document: EP

Kind code of ref document: A1