CN114303054A - Endoscope, fluorescence measuring device, and lens-holding cylindrical body - Google Patents
Endoscope, fluorescence measuring device, and lens-holding cylindrical body Download PDFInfo
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- CN114303054A CN114303054A CN202080061132.9A CN202080061132A CN114303054A CN 114303054 A CN114303054 A CN 114303054A CN 202080061132 A CN202080061132 A CN 202080061132A CN 114303054 A CN114303054 A CN 114303054A
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- excitation light
- endoscope
- fluorescence
- objective lens
- cylindrical body
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Abstract
The invention provides an endoscope which is difficult to obtain fluorescence by being obstructed by body fluid. An endoscope (2) is provided with: an excitation light source (22a) that generates excitation light; an objective lens (L1) that receives fluorescence generated by the Sentinel Lymph Node (SLN) receiving the excitation light; and a cylindrical body (244) that holds an objective lens (L1). The objective lens (L1) is disposed in the center of the cylindrical body (244) inside the cylindrical body (244). For example, the tubular body is arranged in a region of L/3 or more and 2L/3 or less from the sentinel node (SLN) -side end of the tubular body (244) when the length of the tubular body is L. The endoscope (2) is also provided with a collimator lens (L3) that collimates the excitation light.
Description
Technical Field
The present invention relates to acquisition of fluorescence obtained by irradiating an irradiation target (for example, sentinel lymph node or the like) with excitation light in which a fluorescent substance is concentrated.
Background
Conventionally, an endoscope is known that recognizes a lesion or the like (e.g., a malignant tumor or the like) by observing fluorescence obtained by irradiating an irradiation target (e.g., a forward-looking lymph node or the like) with excitation light focused with a fluorescent substance.
For example, patent documents 1, 2, and 3 describe converging collimated light rays, supplying the converged light rays to an optical fiber or a light guide, and supplying the converged light rays to an irradiation target. Patent document 4 describes a case where collimated light is supplied to an irradiation target, unlike patent documents 1 to 3.
Further, patent document 5 describes cleaning of the distal end of an endoscope, patent document 6 describes an endoscope in which a plurality of lenses are arranged in a lens barrel, and patent document 7 describes an endoscope in which fogging is prevented by heating the lenses with a heater. Patent document 8 describes an endoscope in which optical fibers are bundled.
Documents of the prior art
Patent document
Patent document 1: japanese patent laid-open publication No. 2016-120105
Patent document 2: international publication No. 2018-051558
Patent document 3: international publication No. 2016-006371
Patent document 4: japanese patent laid-open publication No. 2007-303990
Patent document 5: japanese patent laid-open publication No. 2009-189496
Patent document 6: japanese laid-open patent publication No. 5-297272
Patent document 7: japanese patent laid-open No. 2006-282
Patent document 8: japanese patent application laid-open No. 2010-158358
Disclosure of Invention
Problems to be solved by the invention
However, according to the above-described conventional technique, the observation of fluorescence is hindered by the adhesion of body fluid to an optical element (for example, an objective lens) located at the distal end of the endoscope and the generation of dirt.
Accordingly, an object of the present invention is to provide an endoscope in which acquisition of fluorescence is difficult due to interference of body fluid.
Means for solving the problems
An endoscope according to the present invention includes: an excitation light source that generates excitation light; an objective lens that receives fluorescence generated by the irradiation object receiving the excitation light; and a cylindrical body that holds the objective lens, the objective lens being disposed in a central portion of the cylindrical body inside the cylindrical body.
According to the endoscope configured as described above, the excitation light source generates excitation light. The objective lens receives fluorescence generated when the irradiation object receives the excitation light. The cylindrical body holds the objective lens. The objective lens is disposed in a central portion of the cylindrical body inside the cylindrical body.
The endoscope of the present invention may further include a collimating section for collimating the excitation light.
In the endoscope of the present invention, when the length of the tubular body is L, the central portion may be a region of L/3 or more and 2L/3 or less from an end portion of the tubular body on the irradiation target side.
The endoscope of the present invention may include: a visible light source that generates visible light; and a multiplexer for multiplexing the visible light and the excitation light.
In the endoscope of the present invention, the collimating section is a lens, and the endoscope includes a mirror that changes a traveling direction of the excitation light transmitted through the collimating section to a direction toward the irradiation target.
The endoscope of the present invention may include a first polarizing plate that transmits the excitation light and a second polarizing plate that transmits the fluorescence, and a transmission axis of the first polarizing plate may be orthogonal to a transmission axis of the second polarizing plate.
The endoscope of the present invention may further include a polarization maintaining fiber that receives the excitation light and supplies the excitation light to the first polarizing plate, and the slow axis or the fast axis of the polarization maintaining fiber may coincide with the transmission axis of the first polarizing plate.
In the endoscope of the present invention, the excitation light source may have a fiber laser.
In the endoscope of the present invention, the excitation light source may further include a wavelength conversion element that converts a wavelength of the fiber laser.
The endoscope of the present invention may include: an excitation light transmission optical fiber that is a single-mode optical fiber for transmitting the excitation light; and a polarization controller that receives the excitation light transmitted through the excitation light transmission fiber, makes a normal direction of a polarization plane of the excitation light orthogonal to a transmission axis of the first polarizing plate, and then supplies the excitation light to the first polarizing plate.
The endoscope of the present invention may include an infrared light source that generates infrared light, and the objective lens may absorb the infrared light.
In the endoscope of the present invention, a surface of the objective lens on the irradiation target side may have a coating layer that reflects the infrared light and transmits the excitation light and the fluorescence.
The endoscope of the present invention may include: a fluorescence-transmitting optical fiber that transmits the fluorescence transmitted through the objective lens; and a fluorescence transmission lens that receives the fluorescence transmitted through the objective lens and supplies the received fluorescence to one end of the fluorescence transmission fiber.
In the endoscope of the present invention, the number of lenses arranged inside the cylindrical body may be only 1 lens.
The fluorescence measuring apparatus of the present invention includes the endoscope of the present invention and a fluorescence measuring unit that measures the fluorescence transmitted through the objective lens.
The lens holding cylindrical body of the present invention includes: an objective lens that receives fluorescence generated by the irradiation object receiving the excitation light; and a cylindrical body that holds the objective lens, the objective lens being disposed in a central portion of the cylindrical body inside the cylindrical body.
Drawings
Fig. 1 shows the configuration of a fluorescence measuring apparatus 1 according to the first embodiment, and optical paths of excitation light and visible light.
Fig. 2 shows the configuration of the fluorescence measuring apparatus 1 according to the first embodiment and the optical paths of fluorescence and reflected light.
Fig. 3 shows the configuration of the fluorescence measuring apparatus 1 according to the second embodiment, and optical paths of the excitation light and the visible light.
Fig. 4 shows the configuration of the fluorescence measuring apparatus 1 according to the second embodiment and the optical paths of fluorescence and reflected light.
Fig. 5 shows the configuration of the fluorescence measuring apparatus 1 according to the third embodiment, and optical paths of the excitation light and the visible light.
Fig. 6 shows the configuration of the fluorescence measuring apparatus 1 according to the third embodiment and the optical paths of fluorescence and reflected light.
Fig. 7 shows the configuration of the fluorescence measuring apparatus 1 according to the fourth embodiment, and optical paths of the excitation light and the visible light.
Fig. 8 shows the configuration of the fluorescence measuring apparatus 1 according to the fourth embodiment and the optical paths of fluorescence and reflected light.
Fig. 9 shows the configuration of the fluorescence measuring apparatus 1 according to the fifth embodiment, and optical paths of the excitation light and the visible light.
Fig. 10 shows the configuration of the fluorescence measuring apparatus 1 according to the fifth embodiment and the optical paths of fluorescence and reflected light.
Fig. 11 is a schematic diagram showing light reflected and transmitted by the coatings TF1, TF2 of the objective lens L1 of the fifth embodiment.
Detailed Description
Hereinafter, embodiments of the present invention will be described with reference to the drawings.
First embodiment
Fig. 1 shows the configuration of a fluorescence measuring apparatus 1 according to the first embodiment, and optical paths of excitation light and visible light. Fig. 2 shows the configuration of the fluorescence measuring apparatus 1 according to the first embodiment and the optical paths of fluorescence and reflected light.
The fluorescence measurement device 1 includes an endoscope 2 and a spectroscope (fluorescence measurement unit) 4. The endoscope 2 is, for example, a laparoscope. The spectroscope 4 is an example of a fluorescence measurement unit that measures fluorescence transmitted through the objective lens L1, and disperses the fluorescence.
The endoscope 2 includes a light source section 22 and a scope section 24.
The light source unit 22 includes an excitation light source 22a, a visible light source 22b, single-mode optical fibers 22c and 22d, a WDM coupler (multiplexer) 22e, and an optical fiber 22 m.
The excitation light source 22a generates excitation light. The excitation light is light irradiated to a sentinel lymph node (irradiation target) SLN having a fluorescent substance. When ICG (indocyanine green) is used as the fluorescent substance, the excitation light is 785nm laser light.
The visible light source 22b generates visible light (e.g., 520nm laser light).
The single-mode optical fiber 22c is connected to the excitation light source 22a and transmits excitation light. The single mode optical fiber 22d is connected to the visible light source 22b and transmits visible light.
The WDM coupler (multiplexer) 22e is coupled to the single-mode optical fiber 22c and the single-mode optical fiber 22d, and multiplexes the excitation light and the visible light. The WDM coupler 22e supplies the combined light obtained by combining the excitation light and the visible light to the optical fiber 22 m.
The optical fiber 22m transmits the combined wave light.
The lens portion 24 includes a connector 242, a cylindrical body 244, a fluorescence transmission optical fiber 246, a connection end 246a, an objective lens L1, a fluorescence transmission lens L2, a collimating lens (collimating portion) L3, a dichroic mirror M1, and a band-pass filter F1.
The fluorescence transmitting fiber 246 transmits the fluorescence transmitted through the objective lens L1 (see fig. 2). The connection end 246a is attached near one end of the fluorescence transmission fiber 246. The fluorescence transmission fiber 246 passes through the connection end 246 a. The other end of the fluorescence transmission fiber 246 is connected to the spectroscope 4.
The connector 242 connects the optical fiber 22m, the cylindrical body 244, and the fluorescence transmission optical fiber 246. The connector 242 houses a dichroic mirror M1, a band-pass filter F1, a fluorescence transmission lens L2, and a collimation lens L3.
The connector 242 has an opening 242a, an opening 242b, an opening 242c, and a connecting end 242 d. The optical fiber 22m is inserted into the opening 242a, and the optical fiber 22m is connected to the connector 242. The cylindrical body 244 is inserted into the opening 242b, and the cylindrical body 244 is connected to the connector 242. A connecting end 242d is attached to the opening 242 c. The connection end portion 246a is inserted into the connection end portion 242d, and the fluorescence transmission optical fiber 246 is connected to the connector 242.
The extending direction of the central axis (optical axis) of the cylindrical body 244 coincides with the extending direction of the central axis (optical axis) of the fluorescence transmission fiber 246. The extending direction of the central axis (optical axis) of the optical fiber 22m is orthogonal to the extending direction of the central axis (optical axis) of the cylindrical body 244.
The cylindrical body 244 holds the objective lens L1. The lenses disposed inside the cylindrical body 244 are only 1 objective lens L1. Further, not only the lens but also an optical element such as a cover glass is not disposed in the cylindrical body 244. Note that no optical element is disposed at the sentinel node SLN-side end of the tubular body 244. The objective lens L1 and the cylindrical body 244 are collectively referred to as a lens holding cylindrical body. WD is a distance between the sentinel lymph node SLN side end of the tubular body 244 and the sentinel lymph node SLN. WD is, for example, 20 to 50 mm.
The objective lens L1 receives fluorescence generated when the sentinel lymph node (irradiation target) SLN receives the excitation light. The objective lens L1 is disposed in the center of the cylindrical body 244 inside the cylindrical body 244. When the length of the tubular body 244 is L (e.g., 300mm), the central portion is a region of L/3 or more and 2L/3 or less from the sentinel lymph node SLN-side end of the tubular body 244.
The central part is shown in fig. 1 and 2, and the other drawings are omitted. However, in any of the embodiments, the objective lens L1 is disposed in the central portion.
The fluorescence transmitting lens L2 receives the fluorescence transmitted through the objective lens L1 and supplies the received fluorescence to one end of the fluorescence transmitting fiber 246 (see fig. 2).
The collimating lens (collimating section) L3 is disposed at a portion slightly on the back side from the opening 242a, receives the excitation light irradiated from one end of the optical fiber 22m, and collimates the excitation light.
The dichroic mirror M1 is disposed at a position where the central axis (optical axis) of the cylindrical body 244 and the central axis (optical axis) of the fluorescence-transmitting optical fiber 246 intersect the central axis (optical axis) of the optical fiber 22M. The dichroic mirror M1 is inclined at 45 degrees (lower on the right) with respect to the central axis (optical axis) of the cylindrical body 244 and the central axis (optical axis) of the optical fiber 22M.
The dichroic mirror M1 changes the traveling direction of the excitation light and the visible light transmitted through the collimating lens L3 by 45 degrees to a direction toward the sentinel lymph node SLN (see fig. 1). The dichroic mirror M1 transmits the fluorescence transmitted through the objective lens L1 (see fig. 2).
The band-pass filter F1 transmits the fluorescence transmitted through the objective lens L1, but does not transmit the reflected light (the excitation light and the visible light reflected by the sentinel lymph node SLN).
Next, the operation of the first embodiment will be described.
First, referring to fig. 1, excitation light is generated from the excitation light source 22a, visible light is generated from the visible light source 22b, and the excitation light and the visible light are multiplexed by the WDM coupler 22e and supplied to the collimating lens L3 via the optical fiber 22 m. The combined light (excitation light and visible light) is collimated by the collimating lens L3, reflected by the dichroic mirror M1, and directed to the sentinel lymph node SLN. The excitation light and the visible light are transmitted through the objective lens L1 to irradiate the sentinel lymph node SLN.
The excitation light and the visible light collimated by the collimating lens L3 are substantially parallel light, and can be regarded as parallel light although they cannot be said to be completely parallel light due to manufacturing errors of the collimating lens L3, the influence of diffraction of light, and the like (the same applies to other embodiments).
Next, referring to fig. 2, since a fluorescent substance is present in the sentinel lymph node SLN, fluorescence is generated when the sentinel lymph node SLN is irradiated with excitation light. The sentinel lymph node SLN reflects excitation light and visible light (reflected light). The fluorescence and the reflected light travel inside the cylindrical body 244, are received by the objective lens L1, and pass through the objective lens L1. The fluorescence further transmits dichroic mirror M1, and reaches fluorescence-transmitting lens L2. The reflected light is reflected by the dichroic mirror M1, but a part of the reflected light transmits through the dichroic mirror M1 and reaches the fluorescence transmission lens L2. The fluorescence transmitting lens L2 receives fluorescence and supplies the fluorescence to one end of the fluorescence transmitting fiber 246. However, the reflected light transmitted through the fluorescence transmitting lens L2 is cut by the band-pass filter F1 and is not supplied to one end of the fluorescence transmitting fiber 246. The fluorescence-transmitting optical fiber 246 transmits the fluorescence to the spectroscope 4. The fluorescence is split by the splitter 4 and measured.
The reflected visible light is acquired by another endoscope not shown, and a video image of the sentinel lymph node SLN is acquired. Thereby, the irradiation range of the excitation light becomes easy to understand (the same applies to other embodiments).
According to the first embodiment, the objective lens L1 is disposed in the central portion of the cylindrical body 244, and therefore is distant from the sentinel lymph node SLN. Therefore, the objective lens L1 is hardly contaminated by the body fluid in the vicinity of the sentinel lymph node SLN, and thus acquisition of fluorescence is hardly hindered by the body fluid. The end of the tubular body 244 on the sentinel lymph node SLN side is easily contaminated with body fluid in the vicinity of the sentinel lymph node SLN, but since no optical element is disposed at this end, acquisition of fluorescence is less likely to be hindered by the body fluid.
When the objective lens L1 is further away from the sentinel lymph node SLN than the central portion of the tubular body 244, the solid angle when the objective lens L1 is observed from a point on the sentinel lymph node SLN becomes too small, and the fluorescence acquisition efficiency becomes too low. Thus, by disposing the objective lens L1 at the central portion of the cylindrical body 244, a decrease in fluorescence acquisition efficiency is suppressed. Since the diameter of the objective lens L1 is substantially equal to the inner diameter of the cylindrical body 244, the solid angle is large even if the objective lens L1 is away from the sentinel lymph node SLN, and the fluorescence acquisition efficiency is good.
Further, according to the first embodiment, since only 1 lens of the objective lens L1 is arranged inside the cylindrical body 244, the cost of the lens holding cylindrical body (the objective lens L1 and the cylindrical body 244) can be reduced. Therefore, the lens holding cylindrical body can be replaced every time the endoscope is used in terms of cost. The lens holding cylindrical body has a simple structure, and therefore, autoclave sterilization treatment can be performed.
Further, according to the first embodiment, since the excitation light is collimated by the collimating lens L3 and then supplied to the sentinel lymph node SLN, the power of the excitation light supplied to the sentinel lymph node SLN can be kept substantially constant regardless of the size of WD. That is, even if WD is large, the power of the excitation light supplied to the sentinel lymph node SLN does not become excessively small, and even if WD is small, the power of the excitation light supplied to the sentinel lymph node SLN does not become excessively large.
Second embodiment
The fluorescence measurement device 1 according to the second embodiment is different from the fluorescence measurement device 1 according to the first embodiment, which includes the single-mode optical fibers 22c and 22d, in that it includes the first polarizing plate PBS1, the second polarizing plate PBS2, and the polarization maintaining optical fibers 22f and 22 g.
Fig. 3 shows the configuration of the fluorescence measuring apparatus 1 according to the second embodiment, and optical paths of the excitation light and the visible light. Fig. 4 shows the configuration of the fluorescence measuring apparatus 1 according to the second embodiment and the optical paths of fluorescence and reflected light. Hereinafter, the same portions as those of the first embodiment are denoted by the same reference numerals, and description thereof is omitted.
The endoscope 2 includes a light source section 22 and a scope section 24.
The light source unit 22 includes an excitation light source 22a, a visible light source 22b, polarization maintaining optical fibers 22f and 22g, a polarization maintaining WDM coupler (multiplexer) 22e1, and a polarization maintaining optical fiber 22m 1.
The excitation light source 22a and the visible light source 22b are the same as those in the first embodiment, and the description thereof is omitted.
The polarization maintaining WDM coupler (combiner) 22e1 is the same as the WDM coupler (combiner) 22e of the first embodiment, but is different in that the polarization maintaining WDM coupler (combiner) 22e1 is of a polarization maintaining type and is joined to the polarization maintaining optical fiber 22f and the polarization maintaining optical fiber 22 g. The polarization maintaining optical fiber 22m1 is the same as the optical fiber 22m of the first embodiment, but is different in the polarization maintaining type.
The polarization maintaining fiber 22f is connected to the excitation light source 22 a. The polarization maintaining fiber 22f receives excitation light from the excitation light source 22a, and supplies the excitation light to the first polarizer PBS1 via the polarization maintaining WDM coupler 22e1 and the polarization maintaining fiber 22m 1. The slow or fast axis of the polarization maintaining fiber 22f coincides with the transmission axis of the first polarizer PBS 1.
The polarization maintaining fiber 22g is connected to the visible light source 22 b. The polarization maintaining fiber 22g receives the excitation light from the visible light source 22b, and supplies the excitation light to the first polarizer PBS1 via the polarization maintaining WDM coupler 22e1 and the polarization maintaining fiber 22m 1. The slow or fast axis of the polarization maintaining fiber 22g coincides with the transmission axis of the first polarizer PBS 1.
The mirror portion 24 includes a connector 242, a cylindrical body 244, a fluorescence transmission optical fiber 246, a connection end 246a, an objective lens L1, a fluorescence transmission lens L2, a collimating lens (collimating portion) L3, a dichroic mirror M1, a band-pass filter F1, a first polarizing plate PBS1, and a second polarizing plate PBS 2.
The connector 242, the cylindrical body 244, the fluorescence transmitting optical fiber 246, the connecting end 246a, the objective lens L1, the fluorescence transmitting lens L2, the collimating lens (collimating section) L3, the dichroic mirror M1, and the band-pass filter F1 are the same as those of the first embodiment, and description thereof will be omitted. However, the connector 242 also houses the first polarizing plate PBS1 and the second polarizing plate PBS 2.
The first polarizing plate PBS1 is disposed between the collimating lens L3 and the dichroic mirror M1. The first polarizing plate PBS1 transmits the excitation light and the visible light (refer to fig. 3).
The second polarizing plate PBS2 is disposed between the band pass filter F1 and one end of the fluorescence transmission fiber 246. The second polarizing plate PBS2 transmits the fluorescence (see fig. 4). More specifically, the fluorescence incident to the second polarizing plate PBS2 is randomly polarized light, and a polarized light component (a component orthogonal to the polarization plane of the excitation light) of the fluorescence that transmits the second polarizing plate PBS2 transmits the second polarizing plate PBS 2.
Wherein the transmission axis of the first polarizer PBS1 is orthogonal to the transmission axis of the second polarizer PBS 2.
Next, the operation of the second embodiment will be described.
First, referring to fig. 3, excitation light is generated from an excitation light source 22a, visible light is generated from a visible light source 22b, and the excitation light and the visible light are multiplexed by a polarization maintaining WDM coupler 22e1 via a polarization maintaining optical fiber 22f and a polarization maintaining optical fiber 22g (both slow axis and fast axis of which coincide with the transmission axis of the first polarizing PBS1), and then supplied to a collimating lens L3 via a polarization maintaining optical fiber 22m 1. The combined light (excitation light and visible light) is collimated by the collimating lens L3, is linearly polarized by the first polarizing plate PBS1, is reflected by the dichroic mirror M1, and is directed to the sentinel lymph node SLN. The excitation light and the visible light are transmitted through the objective lens L1 to irradiate the sentinel lymph node SLN.
Next, referring to fig. 4, since a fluorescent substance is present in the sentinel lymph node SLN, when irradiated with excitation light, fluorescence is generated. The sentinel lymph node SLN reflects the excitation light and the visible light (becomes reflected light). The fluorescence and the reflected light travel inside the cylindrical body 244, are received by the objective lens L1, and pass through the objective lens L1. The fluorescence further transmits dichroic mirror M1, and reaches fluorescence-transmitting lens L2. The reflected light is reflected by the dichroic mirror M1, but a part of the reflected light transmits through the dichroic mirror M1 and reaches the fluorescence transmission lens L2. The fluorescence transmitting lens L2 receives fluorescence and supplies the fluorescence to one end of the fluorescence transmitting fiber 246. The reflected light having passed through the fluorescence transmitting lens L2 is cut off by the band-pass filter F1. As described above, the reflected light transmitted through the band pass filter F1 becomes linearly polarized light by the first polarizing plate PBS1, but cannot transmit the second polarizing plate PBS2 (since the transmission axis of the first polarizing plate PBS1 is orthogonal to the transmission axis of the second polarizing plate PBS 2), and is not supplied to one end of the fluorescence transmission fiber 246. The fluorescence-transmitting optical fiber 246 transmits the fluorescence to the spectroscope 4. The fluorescence is split by the beam splitter 4 and measured.
In this way, the dichroic mirror M1, the band pass filter F1, and the second polarizing plate PBS2 do not provide the excitation light and the reflection of the visible light (reflected light) by the sentinel node SLN to one end of the fluorescence transmitting fiber 246. Part of the excitation light and the visible light is also reflected by the objective lens L1, but they are not supplied to one end of the fluorescence transmission fiber 246, similarly to the reflection (reflected light) of the excitation light and the visible light by the sentinel lymph node SLN, by the dichroic mirror M1, the band pass filter F1, and the second polarizing plate PBS 2.
According to the second embodiment, the same effects as those of the first embodiment are obtained. In addition, according to the second embodiment, since the excitation light and the visible light are linearly polarized light by the first polarizing plate PBS1, the reflected light (the light of the excitation light and the visible light reflected by the sentinel node SLN) transmitted through the band pass filter F1 can be prevented from transmitting through the second polarizing plate PBS2 (the transmission axis of the first polarizing plate PBS1 is orthogonal to the transmission axis of the second polarizing plate PBS 2), and thus can be prevented from being supplied to one end of the fluorescence transmission fiber 246.
Third embodiment
The fluorescence measurement apparatus 1 according to the third embodiment is different from the fluorescence measurement apparatus 1 according to the second embodiment in that the excitation light source 220 includes an optical fiber laser 222 and a PPLN (wavelength conversion element) 224.
Fig. 5 shows the configuration of the fluorescence measuring apparatus 1 according to the third embodiment, and the optical paths of the excitation light and the visible light. Fig. 6 shows the configuration of the fluorescence measuring apparatus 1 according to the third embodiment and the optical paths of fluorescence and reflected light. Hereinafter, the same portions as those of the second embodiment are denoted by the same reference numerals, and description thereof is omitted.
The endoscope 2 includes a light source section 22 and a scope section 24.
The light source unit 22 includes an excitation light source 220, a visible light source 22b, polarization maintaining optical fibers 22f and 22g, a polarization maintaining WDM coupler (multiplexer) 22e1, and a polarization maintaining optical fiber 22m 1. The visible light source 22b, polarization maintaining WDM coupler (combiner) 22e1, polarization maintaining optical fiber 22g, and polarization maintaining optical fiber 22m1 are the same as those in the second embodiment, and description thereof is omitted.
The polarization maintaining fiber 22f is connected to the excitation light source 220.
The excitation light source 220 has a fiber laser 222 and a PPLN (wavelength conversion element) 224.
The fiber laser 222 is an Er-doped continuous oscillation laser having an oscillation wavelength of 1570 nm. The fiber laser has the following preferred characteristics: the output at the oscillation wavelength is high, and if the output is slightly off the oscillation wavelength, the output is abruptly reduced.
The PPLN (wavelength conversion element) 224 is a nonlinear optical element, converts the wavelength of the fiber laser 222 to 1/2 times, and supplies the converted light to the polarization maintaining fiber 22f as 785nm excitation light. The PPLN224 generates 2-order harmonics, thereby converting the wavelength to 1/2-fold.
The mirror portion 24 is the same as that of the second embodiment, and description thereof is omitted.
Next, the operation of the third embodiment will be described.
First, referring to fig. 5, laser light having a wavelength of 1570nm is output from the fiber laser 222 and supplied to the PPLN 224. The PPLN224 generates a 2 nd harmonic of the laser beam having a wavelength of 1570nm, converts the wavelength to 1/2 times, outputs a laser beam having a wavelength of 785nm, and supplies the laser beam to the polarization maintaining fiber 22f as excitation light.
Visible light is generated from the visible light source 22 b. The excitation light and the visible light are multiplexed by the polarization maintaining WDM coupler 22e1 via the polarization maintaining optical fiber 22f and the polarization maintaining optical fiber 22g (both of the slow axis and the fast axis of which coincide with the transmission axis of the first polarizing PBS1), and supplied to the collimating lens L3 via the polarization maintaining optical fiber 22m 1. The combined light (excitation light and visible light) is collimated by the collimating lens L3, becomes linearly polarized light by the first polarizing plate PBS1, is reflected by the dichroic mirror M1, and is directed to the sentinel lymph node SLN. The excitation light and the visible light are transmitted through the objective lens L1 to irradiate the sentinel lymph node SLN.
Next, referring to fig. 6, since a fluorescent substance is present in the sentinel lymph node SLN, when irradiated with excitation light, fluorescence is generated. The sentinel lymph node SLN reflects the excitation light and the visible light (becomes reflected light). The following operation is the same as the operation of the second embodiment described with reference to fig. 4, and the description thereof is omitted.
According to the third embodiment, the same effects as those of the second embodiment are obtained. Further, according to the third embodiment, the output of the excitation light at the oscillation wavelength is high, and when it is slightly deviated from the oscillation wavelength, the output is sharply decreased. Therefore, the excitation light is reflected by the sentinel lymph node SLN (referred to as "reflected light of the excitation light"), and the reflected light reaching the band pass filter F1 has a large component of wavelength 785nm, and the other wavelength components are very small. Therefore, even if the reflected light of the excitation light is not transmitted through the band pass filter F1, the fluorescence to be measured is not significantly cut off, and the transmission of the reflected light of the excitation light is easily prevented.
In the case of using an LED or a semiconductor laser as an excitation light source, the output is not so low even if slightly deviated from the oscillation wavelength. Therefore, it is difficult to prevent transmission of the reflected light of the excitation light by the band-pass filter F1. This is because, when the reflected light of the excitation light slightly shifted from the oscillation wavelength is sufficiently cut off by the band-pass filter F1, the fluorescence to be measured is also greatly cut off because the wavelength of the excitation light is close to the wavelength of the fluorescence.
However, as described above, according to the third embodiment, since the fiber laser 222 is used as the excitation light source, the transmission of the reflected light of the excitation light is easily blocked by the band pass filter F1.
Fourth embodiment
The fluorescence measurement device 1 according to the fourth embodiment is different from the fluorescence measurement device 1 according to the second embodiment in that it includes the polarization controllers 22j and 22k, but does not include the polarization-maintaining fibers 22f and 22 g.
Fig. 7 shows the configuration of the fluorescence measuring apparatus 1 according to the fourth embodiment, and the optical paths of the excitation light and the visible light. Fig. 8 shows the configuration of the fluorescence measuring apparatus 1 according to the fourth embodiment and the optical paths of fluorescence and reflected light. Hereinafter, the same portions as those of the second embodiment are denoted by the same reference numerals, and description thereof is omitted.
The endoscope 2 includes a light source section 22 and a scope section 24.
The light source unit 22 includes an excitation light source 22a, a visible light source 22b, single-mode optical fibers 22c, 22d, 22h, and 22i, a WDM coupler (multiplexer) 22e, polarization controllers 22j and 22k, and an optical fiber 22 m.
The excitation light source 22a, the visible light source 22b, and the WDM coupler 22e are the same as those in the first embodiment, and the description thereof is omitted.
The single-mode fiber (excitation light transmission fiber) 22h is connected to the excitation light source 22a and transmits excitation light. The polarization controller 22j receives the excitation light transmitted through the single-mode optical fiber 22h, and supplies the excitation light to the first polarizing plate PBS1 through the WDM coupler 22e and the optical fiber 22m such that the normal direction of the polarization plane of the excitation light is orthogonal to the transmission axis of the first polarizing plate PBS1 (the excitation light that becomes the polarized light transmits the first polarizing plate PBS 1).
The single mode optical fiber 22i is connected to the visible light source 22b and transmits visible light. The polarization controller 22k receives the visible light transmitted by the single-mode optical fiber 22i, and supplies the visible light to the first polarizing plate PBS1 through the WDM coupler 22e and the optical fiber 22m such that the normal direction of the polarization plane of the visible light is orthogonal to the transmission axis of the first polarizing plate PBS1 (the visible light that becomes the polarized light transmits the first polarizing plate PBS 1).
The single-mode fiber 22c is connected to the polarization controller 22j and transmits excitation light. The single-mode fiber 22d is connected to the polarization controller 22k and transmits visible light.
The mirror portion 24 is the same as that of the second embodiment, and description thereof is omitted.
Next, the operation of the fourth embodiment will be described.
First, referring to fig. 7, excitation light is generated from the excitation light source 22a, and visible light is generated from the visible light source 22 b. The normal directions of the polarization planes of the excitation light and the visible light are orthogonal to the transmission axis of the first polarizing plate PBS1 by the polarization controller 22j and the polarization controller 22 k. The outputs of the polarization controllers 22j and 22k are multiplexed by the WDM coupler 22e and supplied to the collimating lens L3 via the optical fiber 22 m. The combined light (excitation light and visible light) is collimated by the collimating lens L3, becomes linearly polarized light by the first polarizing plate PBS1, is reflected by the dichroic mirror M1, and is directed to the sentinel lymph node SLN. The excitation light and the visible light are transmitted through the objective lens L1 to irradiate the sentinel lymph node SLN.
Next, referring to fig. 8, since a fluorescent substance is present in the sentinel lymph node SLN, when irradiated with excitation light, fluorescence is generated. The sentinel lymph node SLN reflects the excitation light and the visible light (becomes reflected light). The following operation is the same as the operation of the second embodiment described with reference to fig. 4, and the description thereof is omitted.
According to the fourth embodiment, the same effects as those of the second embodiment are obtained.
Fifth embodiment
The fluorescence measuring apparatus 1 according to the fifth embodiment is different from the fluorescence measuring apparatus 1 according to the first embodiment in that it includes an infrared light source 6, and an objective lens L1 has a coating TF 1.
Fig. 9 shows the configuration of the fluorescence measuring apparatus 1 according to the fifth embodiment, and optical paths of the excitation light and the visible light. Fig. 10 shows the configuration of the fluorescence measuring apparatus 1 according to the fifth embodiment and the optical paths of fluorescence and reflected light. Hereinafter, the same portions as those of the first embodiment are denoted by the same reference numerals, and description thereof is omitted.
The endoscope 2 includes a light source section 22, a scope section 24, and an infrared light source 6.
The light source unit 22 is the same as that of the first embodiment, and description thereof is omitted.
The infrared light source 6 generates infrared light.
The lens portion 24 includes a connector 242, a cylindrical body 244, a fluorescence transmitting optical fiber 246, a connecting end 246a, an infrared light transmitting optical fiber 248, a connecting end 248a, an objective lens L1, a fluorescence transmitting lens L2, a collimating lens (collimating portion) L3, a collimating lens L4, dichroic mirrors M1, M2, and a band-pass filter F1.
The infrared light transmission fiber 248 transmits infrared light (see fig. 9). The connection end 248a is attached near one end of the infrared light transmission fiber 248. The infrared light transmission optical fiber 248 passes through the connection end 248 a. The other end of the infrared light transmission fiber 248 is connected to the infrared light source 6.
The connector 242, the cylindrical body 244, the fluorescence transmitting optical fiber 246, the connecting end 246a, the fluorescence transmitting lens L2, the collimating lens (collimating section) L3, the dichroic mirror M1, and the band-pass filter F1 are the same as those of the first embodiment, and the description thereof is omitted.
The connector 242 further houses a collimating lens L4 and a dichroic mirror M2, and further has an opening 242 e. The connection end 248a is inserted into the opening 242e, and the infrared light transmission fiber 248 is connected to the connector 242.
The collimating lens L4 is disposed at a portion slightly on the back side from the opening 242e, receives infrared light from the infrared light transmission fiber 248, and collimates the infrared light. The infrared light collimated by the collimating lens L4 is substantially parallel light, and is not perfectly parallel light due to manufacturing errors of the collimating lens L4, the influence of diffraction of light, and the like, but can be regarded as parallel light.
The direction in which the center axis (optical axis) of the infrared light transmission fiber 248 extends is parallel to the direction in which the center axis (optical axis) of the fluorescent light transmission fiber 246 extends. Therefore, the extending direction of the central axis (optical axis) of the optical fiber 22m is orthogonal to the extending direction of the central axis (optical axis) of the infrared light transmission optical fiber 248.
The dichroic mirror M2 is disposed at a position where the central axis (optical axis) of the infrared light transmission fiber 248 and the central axis (optical axis) of the optical fiber 22M intersect. The dichroic mirror M2 is inclined at 45 degrees (lower right) with respect to the central axis (optical axis) of the infrared light transmitting optical fiber 248 and the central axis (optical axis) of the optical fiber 22M.
The dichroic mirror M2 transmits the excitation light (supplied from the optical fiber 22M) and the visible light, and aligns the traveling direction of the infrared light (supplied from the infrared light transmission fiber 248) with the traveling direction of the excitation light and the visible light (see fig. 9).
The objective lens L1 is similar to the first embodiment, but absorbs infrared light and has coatings TF1 and TF 2.
Fig. 11 is a schematic diagram showing light reflected and transmitted by the coatings TF1 and TF2 of the objective lens L1 of the fifth embodiment.
The objective lens L1 has a coating TF1 on the side of the object (sentinel lymph node SLN) to be irradiated, and this coating TF1 reflects infrared light and transmits excitation light, visible light, fluorescence, and reflected light. The objective lens L1 further includes a coating TF2 on the surface opposite to the irradiation target side, and the coating TF2 transmits infrared light, excitation light, visible light, fluorescence, and reflected light.
Next, the operation of the fifth embodiment will be described.
The operation of the excitation light and the visible light (see fig. 9) is the same as that of the first embodiment (see fig. 1), and the description thereof is omitted. The operation of fluorescence and reflected light (see fig. 10) is also the same as that of the first embodiment (see fig. 2), and the description thereof is omitted. The operation of the infrared light will be described below.
First, referring to fig. 9, infrared light is generated from the infrared light source 6, collimated by the collimating lens L4, reflected by the dichroic mirror M2 toward the dichroic mirror M1, and reflected by the dichroic mirror M1 toward the sentinel lymph node SLN. The infrared light is transmitted through coating TF2 of objective lens L1, but is absorbed by objective lens L1, and the temperature of objective lens L1 rises. The infrared light is reflected by the coating TF1 of the objective lens L1 and not directed towards the sentinel lymph node SLN. The infrared light reflected by the coating TF1 of the objective lens L1 is absorbed by the objective lens L1, and the temperature of the objective lens L1 further rises. A part of the infrared light reflected by the coating TF1 of the objective lens L1 is directed to the fluorescence transmitting optical fiber 246 without being absorbed by the objective lens L1, but cannot pass through the band pass filter F1, and does not enter the fluorescence transmitting optical fiber 246.
According to the fifth embodiment, condensation of the objective lens L1 can be prevented. When the temperature of the abdominal cavity using the endoscope 2 is 36 ℃ and the humidity is 100%, and the temperature of the objective lens L1 is lower than the dew point (about 36 ℃), the objective lens L1 forms dew. Therefore, by heating the objective lens L1 using infrared light, condensation on the objective lens L1 can be prevented.
Since the coating TF1 prevents infrared light from being directed to the sentinel lymph node SLN, side effects (damage to the sentinel lymph node SLN, etc.) caused by infrared light can be prevented. In addition, since the infrared light passes through the coating TF1 and reciprocates in the objective lens L1, the temperature of the objective lens L1 can be increased to a higher level. Further, since the electric wiring for heating the objective lens L1 may not be provided in the objective lens L1, the cost of the lens holding cylindrical body (the objective lens L1 and the cylindrical body 244) can be reduced.
Description of reference numerals
1 fluorescence measuring device
4 spectrometer (fluorescence measuring part)
6 infrared light source
SLN sentinel lymph node (irradiation target)
Length of L-shaped cylinder 244
2 endoscope
22 light source unit
22a excitation light source
22b visible light source
22c, 22d single mode optical fiber
22e WDM coupler (wave combiner)
22e1 polarization maintaining WDM coupler (wave combiner)
22f, 22g polarization maintaining fiber
22h Single mode fiber (fiber for pumping light transmission)
22i single mode optical fiber
22j, 22k polarization controller
22m optical fiber
22m1 polarization maintaining fiber
220 excitation light source
222 fiber laser
224PPLN (wavelength conversion element)
246 optical fiber for fluorescence transmission
Optical fiber for 248 infrared light transmission
24 mirror body part
242 connector
242a, 242b, 242c, 242e
242d connecting end
244 cylinder
246 optical fiber for fluorescence transmission
L1 objective lens
Lens for transmitting L2 fluorescence
L3 collimating lens (collimating unit)
L4 collimating lens
M1, M2 dichroic mirror
F1 band-pass filter
PBS1 first polarizer
PBS2 second polarizer.
Claims (16)
1. An endoscope, comprising:
an excitation light source that generates excitation light;
an objective lens that receives fluorescence generated by the irradiation object receiving the excitation light; and
a cylindrical body that holds the objective lens,
the objective lens is disposed in a central portion of the cylindrical body inside the cylindrical body.
2. The endoscope of claim 1,
the endoscope includes a collimating section that collimates the excitation light.
3. The endoscope of claim 1,
when the length of the cylindrical body is L, the central portion is a region that is L/3 or more and 2L/3 or less from the end portion of the cylindrical body on the irradiation target side.
4. The endoscope of claim 1,
the endoscope is provided with:
a visible light source that generates visible light; and
and a multiplexer for multiplexing the visible light and the excitation light.
5. The endoscope of claim 2,
the collimating part is a lens,
the endoscope includes a mirror that changes a traveling direction of the excitation light transmitted through the collimating section to a direction toward the irradiation target.
6. The endoscope of claim 1,
the endoscope is provided with:
a first polarizing plate that transmits the excitation light; and
a second polarizing plate which transmits the fluorescence,
the transmission axis of the first polarizer is orthogonal to the transmission axis of the second polarizer.
7. The endoscope of claim 6,
the endoscope is provided with a polarization-maintaining optical fiber which receives the excitation light and supplies the excitation light to the first polarizing plate,
the slow axis or the fast axis of the polarization maintaining fiber coincides with the transmission axis of the first polarizer.
8. The endoscope of claim 7,
the excitation light source has a fiber laser.
9. The endoscope of claim 8,
the excitation light source further has a wavelength conversion element that converts the wavelength of the fiber laser.
10. The endoscope of claim 6,
the endoscope is provided with:
an excitation light transmission optical fiber that is a single-mode optical fiber for transmitting the excitation light; and
and a polarization controller that receives the excitation light transmitted through the excitation light transmission fiber, makes a normal direction of a polarization plane of the excitation light orthogonal to a transmission axis of the first polarizing plate, and supplies the excitation light to the first polarizing plate.
11. The endoscope of claim 1,
the endoscope is provided with an infrared light source for generating infrared light,
the objective lens absorbs the infrared light.
12. The endoscope of claim 11,
a coating layer that reflects the infrared light and transmits the excitation light and the fluorescence is provided on a surface of the objective lens on the irradiation target side.
13. The endoscope of claim 1,
the endoscope is provided with:
a fluorescence-transmitting optical fiber that transmits the fluorescence transmitted through the objective lens; and
and a fluorescence transmission lens for receiving the fluorescence transmitted through the objective lens and supplying the received fluorescence to one end of the fluorescence transmission fiber.
14. The endoscope of claim 1,
the lenses arranged inside the cylindrical body are only 1 piece of the objective lens.
15. A fluorescence measurement device is characterized by comprising:
the endoscope of any one of claims 1 to 14; and
and a fluorescence measuring unit that measures the fluorescence transmitted through the objective lens.
16. A lens holding cylindrical body is characterized by comprising:
an objective lens that receives fluorescence generated by the irradiation object receiving the excitation light; and
a cylindrical body that holds the objective lens,
the objective lens is disposed in a central portion of the cylindrical body inside the cylindrical body.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2019172575A JP7198184B2 (en) | 2019-09-24 | 2019-09-24 | Endoscope, fluorescence measurement device and lens holding cylinder |
| JP2019-172575 | 2019-09-24 | ||
| PCT/JP2020/022800 WO2021059611A1 (en) | 2019-09-24 | 2020-06-10 | Endoscope, fluorescence measurement device, and lens-holding cylindrical body |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN114303054A true CN114303054A (en) | 2022-04-08 |
Family
ID=75156593
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202080061132.9A Pending CN114303054A (en) | 2019-09-24 | 2020-06-10 | Endoscope, fluorescence measuring device, and lens-holding cylindrical body |
Country Status (6)
| Country | Link |
|---|---|
| JP (1) | JP7198184B2 (en) |
| KR (1) | KR20220031688A (en) |
| CN (1) | CN114303054A (en) |
| DE (1) | DE112020003560T5 (en) |
| TW (1) | TW202128073A (en) |
| WO (1) | WO2021059611A1 (en) |
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- 2020-06-10 DE DE112020003560.3T patent/DE112020003560T5/en active Pending
- 2020-06-10 WO PCT/JP2020/022800 patent/WO2021059611A1/en active Application Filing
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Also Published As
| Publication number | Publication date |
|---|---|
| KR20220031688A (en) | 2022-03-11 |
| JP7198184B2 (en) | 2022-12-28 |
| JP2021048953A (en) | 2021-04-01 |
| TW202128073A (en) | 2021-08-01 |
| DE112020003560T5 (en) | 2022-05-05 |
| WO2021059611A1 (en) | 2021-04-01 |
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