Optical probe system

Abstract

This optical probe system is characterized by being provided with: a light source that emits first light; an optical probe provided with a first light guide that transmits the first light and irradiates the first light onto a portion to be measured of a subject, and a second light guide that receives and transmits second light, which is return light from the portion to be measured; a sensor that measures the brightness of the second light; and an analyzer that calculates the size of the portion to be measured on the basis of the measurement result of the sensor.

Description

[0001] This application is a divisional application of the Chinese Patent Application No. 202210735407.3, titled "Endoscope and Optical Probe System", filed on June 27, 2022, with priority dates of June 29, 2021, January 18, 2022, and June 17, 2022. TECHNICAL FIELD

[0002] The present application relates to an endoscope and optical probe system capable of evaluating the size of a measurement target portion. BACKGROUND

[0003] In the past, a treatment has been performed in which a calculus such as a gallstone in a body is made fine by being pulverized by laser light or the like from a laser probe and is removed from a body cavity. When such a treatment is performed, there is a demand to evaluate the diameter of the gallstone or the length of a stenosis.

[0004] In the past, an operation has been performed in which the size of a gallstone or a stenosis is evaluated under X-ray observation, for example, with the thickness of an insertion portion of an endoscope (for example, about 10 mm) as a comparative object.

[0005] In Japanese Patent No. 2948615, a plurality of tubes made of X-ray non-transmissive material and a heat shrink tube covering the tubes are disclosed. SUMMARY

[0006] An endoscope of an aspect of the present application includes an insertion portion having a front end forming portion, a powered bending portion disposed on a proximal end side of the front end forming portion, and a lumen disposed along a length axis of the insertion portion, the insertion portion being formed of a resin; an imaging unit provided in the lumen; and a member formed to a prescribed size, provided in the lumen, or embedded in or covered on the outside of the insertion portion, the X-ray transmissivity of the member being different from the X-ray transmissivity of the resin.

[0007] An optical probe system of an aspect of the present application has: a light source that emits first light; an optical probe that has a first light guide that transmits the first light and irradiates the first light toward a measurement target portion of a subject, and a second light guide that receives second light that is return light from the measurement target portion and transmits the second light; a sensor that measures the brightness of the second light; and an analyzer that calculates the size of the measurement target portion based on the measurement result of the sensor. BRIEF DESCRIPTION OF DRAWINGS

[0008] Figure 1 is a diagram showing an endoscope system of a first embodiment of the present application. Figure 2is a perspective view showing the distal end structure of the endoscope of the above-described first embodiment. Figure 3 is a diagram showing the internal structure of the distal end structure of the endoscope of the above-described first embodiment. Figure 4 is a sectional view showing a configuration example in which a treatment instrument elevating platform that changes the direction of a treatment instrument protruding from a treatment instrument channel is provided in the distal end structure of the endoscope in the above-described first embodiment. Figure 5 is a chart showing an example of a member provided at a prescribed position between the distal end of the distal end structure of the insertion section and the proximal end of the active bending section in the above-described first embodiment. Figure 6 is a sectional view showing an example in which a plurality of members are provided on the inner periphery side of the outer member in the above-described first embodiment. Figure 7 is a sectional view and a side view showing an example in which a plurality of members are provided on the outer periphery side of the outer member in the above-described first embodiment. Figure 8 is a side view showing an example in which a member is provided in the treatment instrument channel in the above-described first embodiment. Figure 9 is a perspective view showing a configuration example of the light guide in the above-described first embodiment. Figure 10 is a side view showing an example of a member provided to an optical fiber of two diameters in the above-described first embodiment. Figure 11 is a perspective view showing the distal end structure of the endoscope in a light probe system of a first configuration example of the second embodiment of the present application. Figure 12 is a diagram showing a case in which laser light is irradiated from the first light guide toward a stone and reflected light from the stone is received through the second light guide in the light probe system of the first configuration example of the above-described second embodiment. Figure 13 is a column chart showing an example of the brightness of the emitted light of the laser light and the received reflected light in the first configuration example of the above-described second embodiment. Figure 14 is a coordinate chart showing the relationship between the ratio of the brightness of the reflected light to the brightness of the emitted light of the laser light and the distance from the distal end surface of the insertion section to the stone in the first configuration example of the above-described second embodiment. Figure 15 is a diagram for explaining the positional relationship when imaging the stone in the first configuration example of the above-described second embodiment. Figure 16is a view showing an example of an endoscope image in which an optical image of a subject including a calculus is imaged on an imaging region of an imaging element in the first configuration example of the second embodiment described above. Figure 17 is a view showing a case where excitation light is irradiated to a calculus and fluorescence is received in the optical probe system of the second configuration example of the second embodiment described above. Figure 18 is a view showing a configuration of the optical probe system in which excitation light is emitted from a light source and fluorescence transmitted by a light guide is detected by a sensor in the second configuration example of the second embodiment described above. Figure 19 is a graph showing an example of a relationship between the brightness of fluorescence detected by a sensor and the size of a calculus in the second configuration example of the second embodiment described above. Figure 20 is a view showing the optical probe system in the third configuration example of the second embodiment described above. Figure 21 is a graph showing an example of a brightness distribution with respect to wavelength obtained by spectroscopic analysis of reflected light from a calculus in the third configuration example of the second embodiment described above. Figure 22 is a view showing an insertion portion of an endoscope in the optical probe system of the fourth configuration example of the second embodiment described above. DETAILED DESCRIPTION

[0009] Generally, an endoscope has a reusable endoscope that is used multiple times by being reprocessed, and a disposable endoscope that is used only once. The disposable endoscope is difficult to evaluate the size of a measurement target portion using the thickness of an insertion portion as in the reusable endoscope because X-rays are easily transmitted through since a resin material is used in more parts compared to the reusable endoscope.

[0010] According to the embodiments described below, it is possible to provide an endoscope and an optical probe system that can evaluate the size of a measurement target portion.

[0011] Hereinafter, embodiments of the present application will be described with reference to the accompanying drawings. However, the present application is not limited to the embodiments described below.

[0012] Further, in the description of the drawings, the same reference numerals are attached to the same or corresponding elements as appropriate. In addition, it should be noted that the drawings are schematic and, in order to make the description simple, the relationship of the lengths of the respective elements, the ratio of the lengths of the respective elements, the number of the respective elements, and the like within one drawing are sometimes different from reality. Also, the length relationship or the ratio between a plurality of drawings are sometimes different from each other. [First Embodiment]

[0013] Figures 1 to 10 A first embodiment of the present application will be described below. Figure 1 FIG. 1 is a diagram showing an endoscope system.

[0014] As shown in Figure 1 , the endoscope system 1 is provided with an endoscope 2, a light source device 6, an endoscope control device 7, and a monitor 8.

[0015] The endoscope 2 is provided with an insertion section 3, an operation section 4, and a general-purpose cable 5.

[0016] The insertion section 3 is an elongated section that is inserted into a body lumen of a subject. Further, the subject into which the insertion section 3 is inserted is assumed to be a human body as one example, but is not limited to a human body, and can be a living organism such as an animal, or a non-living organism such as a machine or a building.

[0017] The insertion section 3 is provided with, in order from a distal end side to a proximal end side, a distal end configuration section 3a, an active bending section 3b, and a flexible tube section 3c.

[0018] The endoscope 2 is configured as an electronic endoscope, as shown in Figure 2 , Figure 3 , a camera unit 11 that images a subject is provided inside a lumen in the distal end configuration section 3a. Figure 2 FIG. 2 is a perspective view showing the distal end configuration section 3a of the endoscope 2, Figure 3 FIG. 3 is a diagram showing an internal configuration of the distal end configuration section 3a of the endoscope 2.

[0019] As shown in Figure 3 , the camera unit 11 is provided with an objective optical system 12 in which a plurality of lenses are arranged along an optical axis O, and a camera element 13 that photoelectrically converts an optical image that is imaged by the objective optical system 12 and outputs an electric signal. Inside the insertion section 3, a signal line 14 connected to the camera element 13, a light guide 15 that transmits illumination light, a treatment instrument channel 16 through which a treatment instrument for the endoscope is inserted, and the like are arranged.

[0020] At a distal end face 3al of the distal end configuration section 3a, a distal end of the light guide 15 that irradiates transmitted illumination light toward a subject, a distal end side lens of the objective optical system 12, and a distal end side opening 16a of the treatment instrument channel 16 are arranged.

[0021] The active bending section 3b is a bendable section arranged at the proximal end side of the distal end configuration section 3a. The active bending section 3b is configured to be bendable in two directions or four directions of up and down and left and right, for example.

[0022] As shown in Figure 4As shown, within the active bending portion 3b, a plurality of bending sections 17 are provided so as to be swingable along the length axis of the insertion portion 3, and a bending wire 18 is connected to the bending sections 17 at the front end. The base end of the bending wire 18 is connected to the bending operation knob 4b of the operation portion 4.

[0023] When the active bending portion 3b is bent, the direction of the front end forming portion 3a changes, and the observation direction of the imaging unit 11 and the irradiation direction of the illumination light from the light guide 15 change. Also, the active bending portion 3b is bent in order to improve the insertability of the insertion portion 3 into the subject.

[0024] The flexible tube portion 3c is a tube portion provided on the base end side of the active bending portion 3b and having flexibility.

[0025] The operation portion 4 is provided on the base end side of the insertion portion 3, and has a grip portion 4a, a bending operation knob 4b, and a treatment instrument insertion port 4c. The grip portion 4a is a portion of the endoscope 2 that is held by the palm of the operator's hand. The bending operation knob 4b is an operation device for bending the active bending portion 3b using, for example, the thumb of the hand holding the grip portion 4a. When the bending operation knob 4b is operated, the bending wire 18 is pulled, and the active bending portion 3b is bent. Also, various buttons for operating the endoscope 2 are provided on the operation portion 4. The treatment instrument insertion port 4c is an opening that communicates with the treatment instrument channel 16 and is used for inserting a treatment instrument into the treatment instrument channel 16.

[0026] The general cable 5 extends from, for example, the side of the base end side of the operation portion 4, and a connector 5a for connecting to the light source device 6 and the endoscope control device 7 is provided at the extending end. When the connector 5a is connected to the light source device 6 and the endoscope control device 7, the light guide 15 is connected to the light source device 6, and the signal line 14 is connected to the endoscope control device 7.

[0027] The light source device 6 supplies illumination light to the light guide 15 of the endoscope 2. The light source device 6 has a white light source that emits white illumination light, and also has a special light source that emits special light as needed. As examples of the special light source, there are a laser light source for irradiating a calculus, a light source for exciting light that causes fluorescence to be emitted from a subject, a light source for performing NBI (narrow band light observation), and the like.

[0028] The endoscope control device 7 transmits a driving signal and power to the imaging element 13. The imaging element 13 images the optical image of the subject in accordance with the driving signal, and generates an imaging signal. The imaging performed by the imaging element 13 is performed, for example, sequentially in units of frames, and the imaging signal involved in generating a dynamic image of a plurality of frames. The imaging signal is transmitted to the endoscope control device 7 via the signal line 14.

[0029] The endoscope control device 7 receives the imaging signal obtained by the imaging element 13, performs various image processing such as demosaicing, noise correction, color correction, contrast correction, gamma correction, and the like, and generates an image signal that can be displayed. The endoscope control device 7 can also superimpose various information such as text information or guide information onto the image signal.

[0030] Further, the endoscope control device 7 can also be configured to realize the functions of the respective sections by reading and executing a processing program stored in a storage device (or a recording medium) such as a memory by means of an ASIC (Application Specific Integrated Circuit) including a CPU (Central Processing Unit), a FPGA (Field Programmable Gate Array), or the like. In addition, the endoscope control device 7 can also be configured at least in part as a dedicated electronic circuit.

[0031] The image signal generated by the endoscope control device 7 is output to the monitor 8. The monitor 8 is a display device that accepts the image signal from the endoscope control device 7 and displays the endoscope image.

[0032] Figure 4 is a cross-sectional view showing a configuration example in which the treatment instrument elevating platform 24 that changes the direction of the treatment instrument protruding from the treatment instrument channel 16 is provided at the distal end configuration section 3a of the endoscope 2.

[0033] The distal end section main body 21 is provided at the distal end configuration section 3a, and a cylindrical outer member 22 is provided outside the built-in objects of the insertion section 3 including the distal end section main body 21. The inside of the outer member 22 and the distal end section main body 21 is configured as a lumen, and stores various built-in objects such as the above-described imaging unit 11, the signal line 14, the light guide 15, the treatment instrument channel 16, the bending section 17, the bending wire 18, and the like. Most of the insertion section 3 including the distal end section main body 21, the outer member 22, the light guide 15, and the treatment instrument channel 16 is formed of a raw material such as resin that easily transmits X-rays.

[0034] A housing chamber 23 that communicates with the treatment instrument channel 16 is provided inside the distal end section main body 21. The housing chamber 23 has an opening 23a at one side surface of the distal end configuration section 3a.

[0035] Inside the housing chamber 23, the treatment instrument elevating platform 24 is disposed so as to be rotatable by a support shaft 25. An elevating wire, not shown, is connected to the treatment instrument elevating platform 24, and by pulling the elevating wire, the treatment instrument elevating platform 24 is rotated from the standby position shown by a solid line to the elevating position shown by a double-dotted line.

[0036] When the treatment instrument configured to protrude from the treatment instrument channel 16 is disposed on the treatment instrument elevating platform 24, and the treatment instrument elevating platform 24 is turned to the elevating position, the front end of the treatment instrument is elevated and protrudes from the opening 23a.

[0037] However, the reusable endoscope, which is used multiple times by being reprocessed, is used to evaluate the diameter of a stone or the length of a stricture by comparing the thickness of the insertion portion or the like on an X-ray image with a stone or a stricture.

[0038] In contrast, the disposable endoscope, because a resin material is used in a larger number of portions, is easily transmitted by X-rays (electromagnetic waves having a wavelength of 1 pm to 10 nm), and thus it is difficult to radiograph the insertion portion and difficult to use the thickness of the insertion portion as a comparison object of the size.

[0039] Therefore, a configuration that enables the evaluation of the size even if a large portion of the insertion portion 3 is formed of a resin is described.

[0040] Figure 5 is a chart showing an example in which the member 9 is provided at a predetermined position between the front end of the front end configuration portion 3a and the base end of the active bending portion 3b of the insertion portion 3. The X-ray transmittance of the member 9 is different from that of the resin. The member 9 is formed to a predetermined size.

[0041] In Figure 5 In the example shown, the annular member 9, which is more difficult for X-rays to be transmitted through than the resin, is provided. The member 9 is provided on the front end side of the insertion portion 3 in one or more, and is configured as a ring of metal, for example. However, the member 9 can also be configured as a radio opaque line (X-ray radiographic line). The member 9 is set to a diameter of 10 mm in order to be a comparison object of the size of the measurement target portion, for example. However, in order to enable a more detailed comparison of the size, a member having a diameter of 5 mm can be additionally provided in addition to the member 9 having a diameter of 10 mm.

[0042] Figure 5 Column A of shows an example in which the member 9 is provided at the front end configuration portion 3a.

[0043] Figure 5 Column B of shows an example in which the member 9 is provided at the active bending portion 3b.

[0044] Figure 5 Column C of shows an example in which the member 9 is provided at the front end configuration portion 3a and the active bending portion 3b, respectively.

[0045] Figure 5The column D of FIG. 9 shows an example in which the member 9 is provided at the connecting portion of the active bending portion 3b and the flexible tube portion 3c on the proximal end side. The member 9 can also be constituted by a metal ring, and has a function of reinforcing the connecting portion of the active bending portion 3b and the flexible tube portion 3c.

[0046] Figure 5 The column E of FIG. 9 shows an example in which the member 9 is provided at the connecting portion of the active bending portion 3b and the front end constituting portion 3a on the distal end side. The member 9 can also be constituted by a metal ring, and has a function of reinforcing the connecting portion of the active bending portion 3b and the front end constituting portion 3a.

[0047] Figure 5 The column F of FIG. 9 shows an example in which the member 9 is provided at the connecting portion of the active bending portion 3b and the flexible tube portion 3c on the proximal end side, and a notch 9a such as a V-letter shape is provided in the member 9. The notch 9a is a prescribed shape formed in the member 9, and serves as a mark (icon) indicating a prescribed size of the member 9. The notch 9a can be provided in a number indicating the prescribed size of the member 9. For example, if one is provided, it indicates that the prescribed size of the member 9 is 10 mm, if two are provided, it indicates that the prescribed size of the member 9 is 5 mm, and so on.

[0048] Further, the shape of the notch 9a is not limited to the V-letter shape, but can be a quadrangular shape, or any other arbitrary shape. In addition, the notch 9a can be applied to any one of the members 9 described in the columns A to E of FIG. 9, or to the member 9 described later. Figure 5 Figures 6 to 8 Figure 10

[0049] Since the member 9 is compared with the calculus which is the measurement target portion of the subject, it is preferable that the member 9 be arranged within a range of 30 cm from the distal end of the front end constituting portion 3a.

[0050] Figure 6 FIG. 10 is a cross-sectional view showing an example in which a plurality of members 9 are provided on the inner peripheral side of the outer member 22.

[0051] A lumen is formed in the inside of the cylindrical outer member 22. A plurality of members 9 are embedded on the inner peripheral side of the outer member 22. The plurality of members 9 are, for example, metal rings. The plurality of members 9 are arranged at prescribed intervals in the direction of the length axis of the insertion portion 3 (hereinafter referred to as the axial direction). In the example shown in FIG. 10, for example, five members 9 are arranged in the axial direction. Here, the outer diameter of the member 9 is set to 10 mm, the length in the axial direction is set to 5 mm, and the interval between the adjacent two members 9 is set to, for example, 7.5 mm. By so doing, the size of the calculus can be compared in units of 2.5 mm. Figure 6

[0052] Figure 7 ​​​​These are cross-sectional and side views showing an example of multiple components 9 arranged on the outer periphery of the outer component 22.

[0053] A plurality of components 9 of a predetermined size are disposed on the outer peripheral surface of the outer casing 22. The components 9 covering the outer side of the outer casing 22 are, for example, configured as radio opaque wires. The plurality of components 9 are arranged at predetermined intervals in the axial direction. Figure 7 In the example shown, two components 9 are arranged axially. The axial length of component 9 is, for example, 5 mm. Furthermore, the spacing between the two components 9 can be set to 10 mm, as described above, but it can also be as follows... Figure 7 As shown in column B, it is configured as an indicator of the distance from the front end of the insertion section 3.

[0054] exist Figure 7 In column A, the left side is the front end of insertion part 3. For example... Figure 7 As shown in column B, numerical values ​​are recorded on the two components 9. Each value is configured to be recognizable as text on an X-ray image without the use of radio opacity lines. For example, the component 9 located at the front end of the insertion part 3 is marked with the text "10", and the component 9 located at the base end is marked with the text "20". These characters serve as indicators of the distance from the front end of the insertion part 3; the value "10" indicates a distance of 10 cm from the front end, and the value "20" indicates a distance of 20 cm from the front end.

[0055] Furthermore, if the radio opaque wire is arranged in a loop around the entire circumference, the following situation will occur: Figure 7 The value shown in column B coincides with the half-circumference on the opposite side of the circumference, preventing X-rays from penetrating and making it impossible to identify the text. Therefore, when setting indicators such as text, component 9 can be constructed by setting only half a circumference of the radio opaque line.

[0056] Figure 8 This is a side view showing an example of a component 9 being installed in the treatment device channel 16.

[0057] On, for example, the outer peripheral side of the treatment device channel 16, a plurality of components 9 are arranged axially at predetermined intervals. The plurality of components 9 are metal rings or radio-opaque wires. Figure 7 In the example shown, for instance, three components 9 are arranged axially. By setting the axial length of component 9 to 5 mm and the interval between two adjacent components 9 to, for example, 10 mm, the size of the stone can be compared with the two lengths.

[0058] In addition, such as Figure 2As shown, the annular member 9 can be disposed around the periphery of the imaging unit 11 in the range of the front end forming portion 3a in the axial direction of the insertion portion 3. In the case where the diameter of the imaging unit 11 is, for example, 10 mm or close to 10 mm, the diameter of the member 9 can be set to 10 mm. In the case where the diameter of the imaging unit 11 is, for example, 5 mm or close to 5 mm, the diameter of the member 9 can be set to 5 mm.

[0059] Further, the treatment instrument elevating platform 24 shown in the drawing is formed of a raw material whose X-ray transmittance is different from that of the resin (specifically, lower than that of the resin). For example, the treatment instrument elevating platform 24 can be formed of a metal and formed to have a size and a shape including a prescribed dimension (5 mm, 10 mm, etc.). Figure 4

[0060] Alternatively, the curved section 17 shown in the drawing is formed of a raw material whose X-ray transmittance is different from that of the resin (specifically, lower than that of the resin). For example, the curved section 17 can be formed of a metal and formed to have a size and a shape including a prescribed dimension (5 mm, 10 mm, etc.). At this time, it can be configured that one curved section 17 has a prescribed dimension, or it can be configured that a plurality of curved sections 17 provided in series in the axial direction of the insertion portion 3 are arranged by each prescribed dimension. Figure 4

[0061] is a perspective view showing a configuration example of the light guide 15. Figure 9 The light guide 15 includes an optical fiber 15a having a relatively large diameter and an optical fiber 15b having a relatively small diameter. The outer diameter of the optical fiber 15a is, for example, 1 mm, and the outer diameter of the optical fiber 15b is, for example, 0.3 mm. In the example shown in the drawing, the light guide 15 is formed of two optical fibers 15a and two optical fibers 15b.

[0062] Figure 9

[0063] Figure 10 is a side view showing an example of the member 9 provided to the optical fibers 15a, 15b of two diameters.

[0064] The outer periphery of at least one of the two optical fibers 15a having an outer diameter of 1 mm is provided with the member 9 formed by a metal coating (metal cladding) having a length of 10 mm. The outer periphery of at least one of the two optical fibers 15b having an outer diameter of 0.3 mm is provided with the member 9 formed by a metal coating having a length of 5 mm. At this time, the members 9 provided to the optical fibers 15a are disposed at different positions in the axial direction so that the axial positions do not coincide (that is, so that discontinuous images are reflected on the X-ray image).

[0065] ​​​Further, instead of forming the member 9 by a metal coating, the member 9 can be constituted of an X-ray non-transmissive member such as barium or the like, or an X-ray fluorescent member or the like.

[0066] According to this configuration, the operator of the surgery can confirm the four lengths of 0.3 mm, 1 mm, 5 mm, and 10 mm under X-ray observation, and can finely evaluate the size of the stone by comparing these lengths with the stone.

[0067] According to this first embodiment, by providing the member 9 having an X-ray transmissivity different from that of the resin constituting most of the insertion portion 3, the outline of the member 9 can be clearly confirmed on the X-ray image, and by comparing the outline of the stone as the measurement target portion on the X-ray image, the size of the stone can be evaluated. [Second Embodiment]

[0068] Figures 11 to 22 A second embodiment of the present application is shown. In the second embodiment, the same reference numerals are assigned to the same parts as those of the first embodiment and appropriate description is omitted, and only the differences are mainly described.

[0069] Figures 11 to 16 A first configuration example of the second embodiment is shown, Figure 11 is a perspective view showing the distal end configuration portion 3a of the endoscope 2 in the optical probe system of the first configuration example.

[0070] The optical probe system of the first configuration example is configured as a measurement system using laser light, and has the endoscope 2 as an optical probe. As Figure 11 shown, the endoscope 2 has an objective optical system 12 and a treatment instrument channel 16, and further has a first light guide 15A and a second light guide 15B.

[0071] Figure 12 is a view showing a case where laser light is irradiated from the first light guide 15A toward the stone CA and reflected light from the stone CA is received through the second light guide 15B in the optical probe system of the first configuration example. Figure 13 is a column chart showing an example of the luminance of the outgoing light LA of the laser light and the received reflected light LB in the first configuration example.

[0072] As Figure 12 shown, the optical probe system has a light source 6a that emits laser light, the endoscope 2, a sensor 6b, and an analyzer 7a. For example, the light source 6a and the sensor 6b are provided to a light source device 6, and the analyzer 7a is provided to an endoscope control device 7.

[0073] As Figure 12As shown, the light source 6a emits laser light of a predetermined luminance a1. The first light guide 15A receives the laser light emitted from the light source 6a at the proximal end side and transmits it to the distal end side. The first light guide 15A irradiates the stone CA of the diameter d1 located at a position of an unknown distance D1 with the transmitted laser light as the outgoing light LA from the distal end face 3a1 of the insertion portion 3.

[0074] The outgoing light LA is reflected by the stone CA and generates the reflected light LB as the return light. The second light guide 15B receives the reflected light LB and transmits it to the light source device 6. The reflected light LB is measured for the luminance b1 by the sensor 6b provided in the light source device 6.

[0075] The analyzer 7a acquires the luminance a1 of the outgoing light LA and the luminance b1 of the reflected light LB as shown from the light source device 6, and calculates the luminance ratio b1 / a1. Figure 13

[0076] Figure 14 is a graph showing the relationship between the ratio b / a of the luminance b of the reflected light to the luminance a of the outgoing light of the laser light and the distance D from the distal end face 3a1 of the insertion portion 3 to the stone CA in the first configuration example.

[0077] Generally, the luminance ratio b / a has a correlation with the distance D, and the larger the distance D, the smaller the luminance ratio b / a. Therefore, the graph in which the correlation obtained by the preliminary measurement is plotted with the luminance ratio b / a as the horizontal axis and the distance D as the vertical axis is Figure 14 . The data corresponding to the graph of Figure 14 is stored in advance in the memory in the analyzer 7a.

[0078] The analyzer 7a refers to the graph of Figure 12 and Figure 13 based on the luminance ratio b1 / a1 calculated from the measurement results of Figure 14 to calculate the distance D1 corresponding to the luminance ratio b1 / a1.

[0079] Figure 15 is a graph for explaining the positional relationship when the stone CA is imaged in the first configuration example.

[0080] The field angle θ of the objective optical system 12 of the endoscope 2 is known since it is predetermined by design. The analyzer 7a calculates the width F1 of the imaging range when the distance D1 to the stone CA is measured by irradiating the laser light, for example, as in Numerical Formula 1. [Numerical Formula 1] F1 = 2 x D1 x tan(θ / 2)

[0081] Figure 16 ​is a view showing an example of the endoscope image IMG in which the optical image of the subject including the stone CA in the first configuration example is imaged on the imaging region of the imaging element 13.

[0082] The size of the endoscope image IMG, for example, the width of the endoscope image IMG is set as IF, and the size of the image Ica of the stone CA, which is the measurement target portion of the subject, for example, the diameter of the image Ica is set as Id. According to Figure 15 and Figure 16 , the relationship of Equation 2 is established. [Equation 2] d1 / F1 = Id / IF

[0083] Therefore, the analyzer 7a calculates the actual diameter d1 of the stone CA at the distance D1 as Equation 3. [Equation 3] d1 = F1 x (Id / IF)

[0084] According to the first configuration example, the distance D1 to the stone CA is found based on the intensity ratio of the outgoing light LA and the reflected light LB of the laser light, and the actual diameter d1 of the stone CA can be found from the endoscope image.

[0085] Figures 17 to 19 a second configuration example of the second embodiment is shown, Figure 17 is a view showing a case where the excitation light EL is irradiated to the stone CA and the fluorescence FL is received in the optical probe system of the second configuration example. Figure 18 is a view showing the configuration of the optical probe system in which the excitation light EL is emitted from the light source 6a' and the fluorescence FL transmitted by the light guide 15 is detected by the sensor 6b' in the second configuration example.

[0086] The optical probe system of the second configuration example is configured as a fluorescence measurement system, as Figure 18 is shown, and includes the light source 6a' that emits the excitation light EL, the sensor 6b', the half mirror 6c', and the analyzer 7a'.

[0087] Hereinafter, an example in which the excitation light EL and the transmission of the fluorescence FL use the light guide 15 of the endoscope 2, the light source 6a', the half mirror 6c', and the sensor 6b' are provided in the light source device 6, and the analyzer 7a' is provided in the endoscope control device 7 will be described, but the configuration is not limited to this.

[0088] That is, in the second configuration example, even if the endoscope image is not acquired, the size of the stone CA can be detected. Therefore, instead of the endoscope 2, an optical probe having a light guide can be used to detect the size of the stone CA. In this case, the optical probe system can be configured independently of the endoscope 2, the light source device 6, and the endoscope control device 7. The optical probe can also be inserted through the treatment instrument channel 16 of the endoscope 2.

[0089] When the excitation light EL is emitted from the light source 6a', the excitation light EL is reflected by the half mirror 6c' and is incident on the base end of the light guide 15. As shown in FIG. 6, the excitation light EL transmitted by the light guide 15 is emitted from the front end of the light guide 15 toward the calculus CA. Figure 17

[0090] The calculus CA is excited by the excitation light EL and emits the fluorescent light FL. The fluorescent light FL emitted from the calculus CA is incident on the front end of the light guide 15 and is transmitted by the light guide 15 to be emitted from the base end of the light guide 15. Thus, in the second configuration example, one light guide 15 is enough.

[0091] The fluorescent light FL emitted from the base end of the light guide 15 passes through the half mirror 6c' and the intensity fl of the fluorescent light FL is measured by the sensor 6b'.

[0092] Further, in a case where the return light from the calculus CA includes not only the fluorescent light FL but also the excitation light EL, an excitation light cut filter can be disposed on the optical path between the half mirror 6c' and the sensor 6b'. In addition, in a case where the half mirror 6c' is used, a part of the excitation light EL emitted from the light source 6a' is reflected toward the light guide 15, and the other part is transmitted through the half mirror 6c', and the amount of light emission is wasted. Further, in a case where the half mirror 6c' is used, a part of the fluorescent light FL transmitted by the light guide 15 is transmitted toward the sensor 6b', and the other part is reflected toward the light source 6a', the amount of light of the fluorescent light FL received by the sensor 6b' is reduced, and the sensitivity of the sensor 6b' is decreased. Generally, the wavelengths of the excitation light EL and the fluorescent light FL are different. Therefore, instead of the half mirror 6c', a dichroic mirror or the like that reflects light in the wavelength region of the excitation light EL and transmits light in the wavelength region of the fluorescent light FL can be used.

[0093] Figure 19 is a coordinate diagram showing one example of the relationship between the intensity of the fluorescent light FL detected by the sensor 6b' and the size of the calculus CA in the second configuration example.

[0094] The intensity of the fluorescent light FL emitted when the calculus CA is excited has a correlation with the size of the calculus CA. By measuring the correlation in advance, a coordinate diagram as shown in FIG. 8 can be obtained. Figure 19 Therefore, by calculating the coordinate diagram of the intensity fl of the fluorescent light FL based on the actual measurement, the size dl of the calculus CA can be calculated. Figure 19

[0095] According to the second configuration example, by measuring the intensity of the fluorescent light FL generated when the excitation light EL is emitted toward the calculus CA, the size of the calculus CA can be obtained.

[0096] Figure 20 ​​and Figure 21 Fig. 3 is a diagram showing a third configuration example of the second embodiment. Figure 20 Fig. 4 is a diagram showing a light probe system in the third configuration example. Figure 21 Fig. 5 is a coordinate graph showing an example of a wavelength-dependent luminance distribution obtained by spectroscopic analysis of the reflected light RL from the stone CA in the third configuration example.

[0097] The light probe system of the third configuration example is configured as a stone analysis system, as Figure 20 shown, with a light source 6a", an endoscope 2, a sensor 6b", and an analyzer 7a". For example, the light source 6a" and the sensor 6b" are provided to the light source device 6, and the analyzer 7a" is provided to the endoscope control device 7, but are not limited thereto, and the stone analysis system can be provided independently of the light source device 6 and the endoscope control device 7. In addition, the endoscope 2 is not limited, and a light probe can be used, as in the second configuration example.

[0098] The light source 6a" emits the illumination light IL containing light of a plurality of wavelengths such as white light.

[0099] The endoscope 2 of the third configuration example is provided with the first light guide 15A and the second light guide 15B as in Figure 11 shown. The illumination light IL emitted from the light source 6a" is transmitted by the first light guide 15A, and is irradiated from the front end of the first light guide 15A toward the stone CA.

[0100] The reflected light RL from the stone CA irradiated with the illumination light IL is incident on the front end of the second light guide 15B, and is transmitted by the second light guide 15B.

[0101] The reflected light RL transmitted by the second light guide 15B is incident on the sensor 6b" from the base end of the second light guide 15B. The sensor 6b" is a sensor for spectroscopic analysis, and as Figure 21 shown, measures the luminance of the reflected light RL for each wavelength.

[0102] The spectroscopic analysis result of the sensor 6b" is sent to the analyzer 7a". The analyzer 7a" compares the wavelength-luminance value of the reflected light RL acquired from the sensor 6b" as the spectroscopic analysis result with the wavelength-luminance value of the known stone CA stored in the memory in the analyzer 7a", and determines the kind of the stone CA (for example, which of cholesterin stones, mixed stones, pigment stones, and the like it belongs to). The kind of the stone determined by the analyzer 7a" is displayed on the monitor 8, for example, together with the endoscope image.

[0103] The operator of the surgery confirms the kind of the specific stone by watching the monitor 8, and can select which pulverization method to use to pulverize the stone CA.

[0104] According to the third configuration example, assistance for a surgical operator to select a crushing method of the stone CA can be performed.

[0105] Figure 22 Fig. 6 is a view showing an insertion section 3 of an endoscope 2 in a light probe system according to a fourth configuration example of the second embodiment.

[0106] The light probe system of the fourth configuration example is provided with, for example, the endoscope 2 as the light probe. However, a light probe not provided with an imaging function can be used instead of the endoscope 2.

[0107] The endoscope 2 (or the light probe) is provided with a suction passage. Here, the description is made assuming that the treatment instrument passage 16 functions as the suction passage, but the suction passage can be provided independently of the treatment instrument passage 16.

[0108] Laser light transmitted by the light guide 15 functioning as a laser light guide is irradiated to the stone CA from the front end of the light guide 15 disposed at the front end surface 3al of the insertion section 3.

[0109] A protruding shape section 3a2 protruding forward of the front end surface 3al is provided at the front end of the insertion section 3. The front end opening of the treatment instrument passage 16 functioning as the suction passage is disposed at the protruding shape section 3a2.

[0110] Since the stone CA is movable, it can be difficult to accurately irradiate laser light to the stone CA or to perform recovery of the stone CA.

[0111] Therefore, in the fourth configuration example, the stone CA can be more reliably crushed and recovered by using the following method.

[0112] First, the stone CA is fixed to the front end opening of the treatment instrument passage 16 functioning as the suction passage by performing suction from the treatment instrument passage 16. The fixed stone CA does not move and is fixed to the protruding shape section 3a2 further forward than the front end surface 3al, and thus, when laser light is irradiated from the front end of the light guide 15, the stone CA can be reliably crushed. The stone CA crushed and finely fragmented is directly recovered from the treatment instrument passage 16 in which suction is being performed.

[0113] Further, in the case where the stone CA is an organic stone, a part of the stone CA can be melted when laser light is irradiated. Therefore, in the case where the light probe is used, the following method can also be adopted: the stone CA is recovered by bringing the melted stone CA into contact with the light probe, and the light probe is pulled out after the melted part is cooled and solidified. The specific method of bringing the melted stone CA into contact with the light probe at this time is, for example, the following method.

[0114] In the first method, laser light is irradiated to melt the stone CA, and the front end of the optical probe is brought close to the stone CA to bring the stone CA into contact with the front end of the optical probe.

[0115] In the second method, laser light is irradiated to pulverize the stone CA while melting it, and suction is performed by the suction channel to bring the stone CA into contact with the front end opening of the suction channel.

[0116] In the third method, the stone CA is brought into contact with the front end opening of the suction channel by suction performed by the suction channel, the state of contact is maintained, laser light is irradiated to melt the stone CA, and the melted portion is solidified.

[0117] By employing these methods, it is also possible to reliably recover a large stone CA that is difficult to recover by the suction channel.

[0118] According to such a second embodiment, in an optical probe system using light such as laser light, excitation light, etc., it is also possible to evaluate the size of the stone CA as a measurement target portion. Further, by performing spectroscopic analysis, it is possible to determine the kind of the stone CA. Moreover, by suctioning the stone by the suction channel, it is possible to reliably pulverize the stone CA. Further, by bringing the stone CA melted due to irradiation of laser light into contact with the optical probe to solidify it, it is possible to reliably recover the stone CA.

[0119] Further, the present application is not limited to the above-described embodiments, and in the implementation stage, the constituent elements can be deformed and embodied within the scope of the gist thereof. Further, by appropriately combining a plurality of constituent elements disclosed in the above-described embodiments, various inventive concepts can be formed. For example, several constituent elements can be deleted from all the constituent elements shown in the embodiments. Moreover, the constituent elements in different embodiments can be appropriately combined. In this way, various modifications or applications can be made within the scope of the gist of the present application, of course.

Claims

1. An optical probe system, characterized in that, have: The light source, which emits the first light; A light probe having a first light guide and a second light guide, wherein the first light guide transmits the first light and irradiates the measurement target portion of the test subject, and the second light guide receives the second light as return light from the measurement target portion and transmits the second light. The sensor measures the brightness of the second light mentioned above; and The analyzer calculates the size of the measured object based on the measurement results of the sensor.

2. The optical probe system according to claim 1, wherein, The aforementioned optical probe is an endoscope equipped with a camera unit that can capture images of the subject being examined. The first optical guide and the second optical guide mentioned above are configured separately. The first light mentioned above is a laser with a specified brightness, and the second light mentioned above is the reflected light of the laser that has been partially reflected by the object being measured. The aforementioned sensor measures the brightness of the reflected light. The analyzer calculates the distance to the measured object portion from the ratio of the brightness of the laser to the brightness of the reflected light. Based on the calculated distance, the field of view of the camera unit, and the ratio of the size of the endoscope image acquired by the camera unit to the size of the measured object portion in the endoscope image, the analyzer calculates the size of the measured object portion.

3. The optical probe system according to claim 1, wherein, The first optical guide mentioned above and the second optical guide mentioned above are the same. The first light mentioned above is the excitation light, and the second light mentioned above is the fluorescence emitted by the measured object. The sensor described above measures the brightness of the fluorescence. The analyzer calculates the size of the measured object based on the brightness of the fluorescence.

4. The optical probe system according to claim 1, wherein, The first light mentioned above is illumination light containing multiple wavelengths, and the second light mentioned above is reflected light from the illumination light that has been partially reflected by the object being measured. The aforementioned sensor measures the brightness of the reflected light at each wavelength. The analyzer determines the type of the measured object based on the measurement results of the sensor.

5. The optical probe system according to claim 1, wherein, The aforementioned optical probe also has an attraction channel. The first optical guide mentioned above and the second optical guide mentioned above are the same laser optical guide. The front opening of the aforementioned attraction channel is located in a protruding shape that protrudes forward from the front end of the aforementioned laser light guide.

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