JP4185313B2 - Fluorescence measuring device - Google Patents

Description

[0001]
BACKGROUND OF THE INVENTION
The present invention relates to a fluorescence measuring apparatus that acquires information for diagnosis by an operator based on autofluorescence emitted from a living tissue.
[0002]
[Prior art]
Conventionally, it is known that when excitation light (ultraviolet light) is irradiated to a living tissue, the living tissue is excited and emits fluorescence (autofluorescence). Furthermore, it is known that autofluorescence emitted from a living tissue in which a lesion such as a tumor occurs has a property different from fluorescence emitted from a normal living tissue. In particular, the intensity of the green band component in autofluorescence from the lesioned tissue is lower than that from normal tissue. However, the intensity of the red band component in autofluorescence from the lesioned tissue is comparable to that from normal tissue. Therefore, the ratio between the intensity of the green band and the intensity of the red band of autofluorescence from the lesioned tissue is smaller than that from normal tissue.
[0003]
Therefore, as a useful information for diagnosis (diagnostic information), a fluorescence diagnostic system that measures the ratio of the intensity of the green band of the autofluorescence to the intensity of the red band and provides it to the operator has been developed. Yes. FIG. 8 is a graph showing characteristics of excitation light and light to be measured. The horizontal axis of the graph of FIG. 8 indicates the wavelength of light, and the vertical axis indicates the intensity. The excitation light is ultraviolet light having an intensity peak at the wavelength λe. This wavelength λe is set to λe = 365 nm, for example. Then, the first wavelength band centered on the wavelength λ1 and the second wavelength band centered on the wavelength λ2 in autofluorescence are measured. These wavelengths λ1 and λ2 are set in the above-described green band and red band, respectively. Therefore, λ1 <λ2.
[0004]
The fluorescence diagnostic system includes a probe and a fluorescent diagnostic auxiliary device. The probe is configured by bundling a number of irradiation optical fibers that guide excitation light and a number of detection optical fibers that guide fluorescence. The probe is detachably connected to the fluorescent diagnosis auxiliary device via a connector provided on the base end side.
[0005]
The auxiliary apparatus for fluorescence diagnosis includes an excitation light source unit that emits excitation light and a detection unit that detects light from a living body. Then, the excitation light emitted from the excitation light source unit in a state where the probe is connected to the fluorescence diagnostic auxiliary device is incident from the proximal end surface of the irradiation optical fiber of the probe, is emitted from the distal end, and is detected light. Light incident from the tip of the fiber and emitted from the base end face is detected by the detector.
[0006]
Usually, this probe is used by being pulled from its tip into the forceps channel of the endoscope. Specifically, an operator who uses these probes and an endoscope makes the distal end of the endoscope face the subject, the distal end of the probe protrudes from the distal end of the endoscope, and comes into contact with the subject. . In this state, the excitation light emitted from the tip of the optical fiber for irradiation of the probe to the subject excites the living body of the subject and emits autofluorescence. For this reason, this autofluorescence enters the tip of the probe together with the excitation light reflected from the surface of the subject. Among these, the light (detection light) incident on the detection optical fiber constituting the probe is detected by the detection unit through the filter that cuts the excitation light component.
[0007]
Thereafter, the ratio between the intensity of the green band and the intensity of the red band of the detection light is calculated and displayed on the monitor. The surgeon determines that the subject is normal if the intensity ratio is large, and determines that a lesion is present in the subject if the intensity ratio is small. As a result, it is possible to perform accurate measurement that excludes the influence of the intensity of excitation light and the fluorescence emission intensity that differs for each part of the subject.
[0008]
[Problems to be solved by the invention]
However, since the fluorescence emitted from the living body is weak, it takes a certain amount of time to receive the amount of fluorescence necessary for measurement. Therefore, the tip of the probe may deviate from the subject measurement target site while receiving the amount of fluorescence necessary for measurement. If the tip of the probe deviates from the measurement target part of the subject during light reception in this way, the data obtained as a result of the measurement will no longer accurately indicate the state of the measurement target part, and errors will occur. It is only something that includes a lot.
[0009]
The present invention has been made in view of the problem of such a conventional fluorescence observation probe, and the problem is that the fluorescence measurement in which the tip of the probe does not deviate from the measurement target site while receiving fluorescence from the subject. The provision of the device.
[0010]
[Means for Solving the Problems]
The fluorescence measuring apparatus according to the present invention employs the following configuration in order to solve the above problems.
[0011]
That is, the fluorescence measuring apparatus according to the present invention is an apparatus for analyzing fluorescence generated from a living tissue of a subject by irradiating the subject with excitation light. It is comprised from the apparatus main body connected with a base end. The probe includes first and second light guides and suction pipes connecting the tip surface and the apparatus main body, and the tip edge projects beyond the tip surface to A hood made of a cylindrical elastic member attached airtightly in a state of surrounding the distal end surface is provided. The apparatus main body includes an excitation light source that introduces excitation light into the first light guide, a light receiving unit that receives fluorescence guided by the second light guide, and suction that performs suction through the suction pipe. The probe tip surrounded by the hood by sucking air from the tip surface of the probe through the suction pipe by the suction means in a state where the tip of the hood is in close contact with the surface of the subject. The space between the surface and the subject surface is evacuated, and the probe hood is brought into close contact with the subject surface by being deformed while the hood is kept in close contact with the subject surface. It is characterized by preventing it from coming off the surface.
[0012]
If comprised in this way, a suction means can attract | suck air from the front end surface of a probe through a suction pipe. Therefore, when the tip of the hood is in close contact with the subject surface, the space between the probe tip surface surrounded by the hood and the subject surface is exhausted, so that the hood remains in close contact with the subject surface. By deforming the probe, the probe tip surface is brought into close contact with the subject surface, and the probe tip is not detached from or displaced from the subject surface. If the light source device introduces excitation light into the first light guide while maintaining this state, excitation light is emitted from the probe tip surface that is in close contact with the subject surface, and the biological tissue of the subject is excited. And fluorescence is generated from the living tissue. This fluorescence is guided by the second light guide, received by the light receiving means, and analyzed. Therefore, since the tip of the probe does not deviate from the measurement target site of the subject while the fluorescence is measured, the measurement result accurately indicates the state of the measurement target site.
[0013]
DETAILED DESCRIPTION OF THE INVENTION
Hereinafter, an embodiment of the present invention will be described with reference to the drawings. FIG. 1 is a schematic configuration diagram schematically showing the fluorescence diagnostic system of the present embodiment. This fluorescent diagnostic system includes an electronic endoscope (hereinafter abbreviated as an endoscope) 1, a light source processor device 2, a probe 5, a fluorescent diagnostic auxiliary device (hereinafter abbreviated as a diagnostic auxiliary device) 3, and a monitor 4. Have.
[0014]
<Endoscope>
First, the endoscope 1 will be described. The endoscope 1 has a flexible tubular insertion portion that is inserted into a living body. However, the detailed shape of the endoscope 1 is not shown in FIG. A bending portion is incorporated at the distal end of the insertion portion, and a distal end portion made of a hard member is fixed to the distal end of the bending portion. An operation unit is coupled to the proximal end of the insertion unit. The operation portion is provided with a dial and various operation switches for bending the bending portion.
[0015]
At least three through holes are formed in the distal end portion of the endoscope 1, and a light distribution lens 11 and an objective lens 12 are fitted in the pair of through holes, respectively. The other one through hole is used as the forceps hole 13. Specifically, a tube connecting this forceps hole 13 and an opening (base forceps forceps hole 14) opened in the operation portion is passed through the endoscope 1, and both forceps holes are passed through this tube. A tube formed between 13 and 14 is used as a forceps channel.
[0016]
Furthermore, the endoscope 1 has a light guide 15. The light guide 15 is a fiber bundle in which a large number of optical fibers are bundled. The light guide 15 is passed through the endoscope 1 with its distal end faced to the light distribution lens 11, and its proximal end is passed through the light source processor device 2.
[0017]
Furthermore, the endoscope 1 has an image sensor 16 formed of a CCD area sensor. The imaging surface of the imaging element 16 is disposed in the vicinity of a position where the objective lens 12 connects the subject images when the distal end portion of the endoscope 1 is disposed to face the subject. The image sensor 16 acquires image data based on the subject image and outputs the image data to the signal line 17.
[0018]
<Light source processor device>
Next, the light source processor device 2 will be described. The light source processor device 2 includes a system controller 21 and a timing generator 22 connected to each other. The system controller 21 is a controller that controls the entire light source processor device 2. The timing generator 22 is a circuit that generates various reference signals, and various processes in the light source processor device 2 proceed according to the reference signals.
[0019]
Further, the light source processor device 2 includes a white light source 23 and a condenser lens 24. The white light source 23 emits white light as parallel light. The condenser lens 24 is disposed on the optical path of white light emitted from the white light source 23, and converges the white light on the base end surface of the light guide 15.
[0020]
A wheel 25 is inserted on the optical path between the condenser lens 24 and the light guide 15. The wheel 25 has a disk-shaped outer shape, and three openings are provided in a ring-shaped region along the outer periphery thereof. Each of these openings is fitted with an R filter that transmits only the red band of incident light, a G filter that transmits only the green band, and a B filter that transmits only the blue band.
[0021]
The center of the wheel 25 is fixed with respect to the output shaft of the motor 25M. The motor 25M is connected to the timing generator 22. Then, the motor 25M inserts the R filter, G filter, and B filter of the wheel 25 sequentially and repeatedly into the optical path between the condenser lens 24 and the light guide 15 in accordance with the reference signal from the timing generator 22. Then, the wheel 25 is rotated.
[0022]
Then, red light (R light), green light (G light), and blue light (B light) sequentially and repeatedly enter the base end face of the light guide 15. The incident R light, G light, and B light are guided to the light guide 15, diffused by the light distribution lens 11, and illuminate the subject facing the distal end of the endoscope 1. Then, on the imaging surface of the imaging element 16, an image of the subject by R light, an image by G light, and an image by B light are sequentially formed. The imaging element 16 converts the image of the subject by R light, the image by G light, and the image by B light, respectively, into image signals and sequentially outputs them to the signal line 17.
[0023]
Further, the light source processor device 2 includes one pre-processing unit 26, three memories 27R, 27G, and 27B, and three post-processing units 28R, 28G, and 28B connected to the timing generator 22, respectively. The pre-stage processing unit 26 is connected to the signal line 17 and sequentially acquires the image signals output from the image sensor 16, performs signal processing and A / D conversion, and outputs them as digital image data. Each memory 27R, 27G, and 27B is connected to the pre-processing unit 26, respectively. Then, according to the reference signal input from the timing generator 22 to each of the memories 27R, 27G, and 27B, the digital image data output from the pre-processing unit 26 at the time of R light irradiation is stored in the memory 27R as R image data, and at the previous stage at the time of G light irradiation. The digital image data output from the processing unit 26 is stored in the memory 27G as G image data, and the digital image data output from the pre-processing unit 26 at the time of B light irradiation is stored in the memory 27B as B image data.
[0024]
Respective post-processing units 28R, 28G, 28B are connected to the memories 27R, 27G, 27B, respectively. The post-processing units 28R, 28G, and 28B sequentially read out the R image data, G image data, and B image data stored in the memories 27R, 27G, and 27B, respectively, and perform signal processing and D / A conversion. Thus, an R image signal, a G image signal, and a B image signal, which are analog image signals, are output. The output R image signal, G image signal, and B image signal are output to a video output terminal (not shown) as a set of video signals together with a synchronization signal (Sync) output from the timing generator 22.
[0025]
The system controller 21 stops the light emission of the white light source 23 and stops the operation of the timing generator 22 while being instructed to turn off the white light source 23 from a system control circuit 30 (to be described later) of the diagnostic auxiliary device 3. Let
[0026]
The monitor 4 is connected to the video output terminal, acquires the output video signal, and displays it on the screen. That is, the monitor 4 displays a moving image of the color image of the subject.
[0027]
<Probe>
Next, the probe 5 will be described. As shown in FIG. 1, the probe 5 has an outer diameter that can be inserted into the forceps channel of the endoscope 1 and has an entire length sufficiently longer than the entire length of the forceps channel, The connector 51 is fixed to the base end and is removably inserted into a connector receiver 31 (to be described later) of the diagnostic auxiliary device 3.
[0028]
FIG. 3 is a front view showing the distal end surface of the insertion portion 50 of the probe 5, and FIG. 4 is a longitudinal sectional view of the vicinity of the distal end of the insertion portion 50 along the IV-IV line in FIG. As shown in these drawings, the insertion portion 50 includes a slightly larger diameter excitation light light guide 501, four slightly smaller diameter fluorescent light guides 502, and a fluorescent light guide 502. The four suction pipes 503 having substantially the same diameter are built in a silicon tube 504 having a certain degree of flexibility and buckling resistance. The excitation light guide 501 as a first light guide is composed of a bundle (fiber bundle) of a large number of quartz optical fibers (or plastic optical fibers) having excellent transmittance for ultraviolet rays. Similarly, each of the fluorescent light guides 502 as the second light guides is composed of a bundle (fiber bundle) of a plurality of quartz optical fibers (or plastic optical fibers). However, the fluorescent light guides 502 are grouped into a single fiber bundle in the vicinity of the proximal end thereof. Further, the tip of each suction pipe 503 is closed by a film 505 having excellent air permeability and water repellency such as a polytetrafluoroethylene film having a continuous porous structure.
[0029]
The built-in object described above is freely movable in the silicon tube 504 except for the tip of the insertion portion 50. However, at the tip of the insertion portion 50, around the light guide 501 for excitation light, The fluorescent light guide 502 and the suction pipe 503 are fixed alternately. Further, at the distal end of the insertion portion 50, the gap between the built-in objects is sealed to keep the inside of the probe 5 liquid-tight and air-tight. Thereby, the front-end | tip of the insertion part 50 takes a cylindrical shape.
[0030]
In addition, a spacer ring 506 made of a cylindrical rubber member is fitted on the outer periphery of the distal end of the insertion portion 50 with the distal end edge aligned with the distal end of the insertion portion 50. And between the outer peripheral surface of the silicon tube 504 which comprises the insertion part 50, and the inner peripheral surface of the spacer ring 506, it adhere | attached airtight with the adhesive agent. Further, on the outer periphery of the spacer ring 506, a hood 507 made of a cylindrical rubber member (elastic member) having the same inner diameter as the outer diameter of the spacer ring 506 has a leading edge that is more than the leading edge of the spacer ring 506. It is fitted in a protruding state. The outer peripheral surface of the spacer ring and the inner peripheral surface of the hood 507 are hermetically bonded with an adhesive.
[0031]
On the other hand, the connector 51 is made of a hard member such as plastic, and has a cylindrical shape whose end is narrowed by one step as shown in FIG. Further, in this connector 51, a through hole 51a for airtightly passing the excitation light light guide 501, a through hole 51b for airtightly penetrating the fluorescent light guide 502 combined into one, and Four through holes 51c for penetrating each suction pipe 503 in an airtight manner are formed. Among these through holes 51 a to 51 c, through holes 51 a and 51 b for penetrating the light guides 501 and 502 pass through the small diameter portion 510 and reach the end face of the connector 51. On the other hand, the through holes 51c for allowing the suction pipes 503 to pass therethrough are open in the vicinity of the end portion of the outer peripheral surface of the small diameter portion 510.
[0032]
Further, an O-ring 511 having an outer diameter slightly smaller than the outer diameter of the large-diameter portion is fitted into the step portion of the small-diameter portion 510 of the connector 51 with respect to the large-diameter portion.
[0033]
Note that a key for rotational positioning is preferably formed on the outer peripheral surface of the large-diameter portion of the connector 51 in parallel with its axis.
[0034]
<Auxiliary device for diagnosis>
Next, the diagnostic auxiliary device 3 as the apparatus main body of the fluorescence measuring device will be described. First, the mechanical structure of the connector receiver 31 to which the connector 51 of the probe 5 described above is attached will be described.
[0035]
The connector receiver 31 is constructed on the side surface of the casing of the diagnostic auxiliary device 3. More specifically, the connector receiver 31 is integrally attached to the inner surface of the casing so as to open on the side surface of the casing. The connector receiver 31 as a whole has a bottomed cylindrical shape having an inner diameter substantially the same as the outer diameter of the large diameter portion of the connector 51. However, when a key is formed on the outer peripheral surface of the connector 51, a key groove for rotationally positioning the connector 51 by engaging with the key is formed on the inner peripheral surface of the connector receiver 31. Need to be. Note that the key and the keyway may be reversed.
[0036]
In addition, a flange member 310 that is a ring having a rectangular cross-section having an inner diameter slightly larger than the outer diameter of the narrow-diameter portion 510 of the connector 51 and having the same outer diameter as the inner diameter of the connector receiver 31 is provided in the middle of the connector receiver 31. However, it is inset. The outer surface of the flange member 310 and the inner surface of the connector receiver 31 are hermetically bonded with an adhesive. An O-ring 511 as a seal member fitted to the connector 51 abuts against the outer end surface of the flange member 310 and is slightly crushed, whereby the space in the connector receiver 31 is sealed and the connector 51 is positioned. Therefore, the flange member 310 is fixed to the connector receiver 31 so that a predetermined distance is secured between the end surface of the connector 51 positioned thereby and the bottom surface of the connector receiver 31.
[0037]
Between the flange member 310 on the inner peripheral surface of the connector receiver 31 and the bottom surface, a pressure sensor 32 for detecting the atmospheric pressure of the inner space of the connector receiver 31 sealed by the O-ring 511 is attached. An exhaust pipe 311 connected to a pump 33 for sucking the space in 31 is opened. A purge valve 34 that opens the space in the connector receiver 31 to the atmosphere is provided between the connector receiver 31 and the pump 33 in the exhaust pipe 311. The exhaust pipe 311, the pump 33 and the purge valve 34 constitute a suction means.
[0038]
Furthermore, the condenser lens 312 and the collimator lens 313 that are opposed to the excitation light guide 501 and the fluorescence light guide 502 on the end face of the connector 51 positioned as described above are fitted into the bottom surface of the connector receiver 31. ing.
[0039]
Behind the condenser lens 312 is disposed a UV lamp 35 as an excitation light source that emits excitation light that is focused on the end face of the excitation light guide 501 by the condenser lens 312.
[0040]
On the optical axis of the collimator lens 313, an excitation light cut filter 36, a rotation filter 37, and a first detector 38 are installed in that order. The excitation light cut filter 36 cuts only the excitation light (ultraviolet light component) from the light emitted from the end face of the fluorescence light guide 502 and converted into parallel light by the collimator lens 313, and only the fluorescence (visible light component). Transparent. The rotary filter 37 is a disk-like filter that is rotationally driven by a motor 39 around a rotation axis parallel to the optical axis of the collimator lens 313. As shown in the front view of FIG. Are separated into a λ1 region that transmits only a fluorescent component (green light component) having a wavelength of λ1 and a λ2 region that transmits only a fluorescent component (red light component) having a wavelength of λ2. ing. The rotation filter 37 is arranged at a position where the λ1 region and the λ2 region are alternately inserted in the fluorescence optical path transmitted through the excitation light cut filter 36 along with its rotation. The first detector 38 as a light receiving means receives the fluorescence transmitted through each region (λ1 region or λ2 region) of the rotary filter 37 and outputs a signal corresponding to the intensity of the received fluorescence.
[0041]
Note that a second detector 40 that detects the rotation angle of the rotary filter 37 is attached to the motor 39. The second detector 40 has a signal corresponding to a region (λ1 region or λ2 region) inserted in the fluorescence optical path (that is, a logical value “in the angular range where the λ1 region is inserted in the fluorescence optical path”). In the angle range in which the 1 ″ and λ2 regions are inserted in the optical path of fluorescence, a digital signal having a logical value “0” is output.
[0042]
The output signal of the first detector 38 described above (that is, an analog signal corresponding to the intensity of received fluorescence) is amplified with a constant gain by the amplifier 41 and then converted into a digital signal by the first A / D converter 42. Are input to the system control circuit 30.
[0043]
Further, the output signal of the pressure sensor 32 (that is, an analog signal indicating the detected atmospheric pressure) is converted into a digital signal (an 8-bit signal having a value of 0 to 256) by the second A / D converter 43, and system control is performed. Input to the circuit 30.
[0044]
On the other hand, the output signal of the second detector 40 is directly input to the system control circuit 30.
[0045]
On the other hand, the motor 39, the purge valve 34, and the pump 33 described above are driven by currents supplied from the first driver 43, the second driver 44, and the third driver 45 that operate according to the control by the system control circuit 30, respectively.
[0046]
The UV lamp 35 is driven by the current output from the lamp power supply 48 whose output current value is adjusted by the intensity control circuit 47 controlled by the system control circuit 30. Note that a lamp containing an excitation light component can be substituted for the UV lamp 35. In this case, a filter that transmits only the excitation light component is inserted between the lamp and the condenser lens 312. There is a need.
[0047]
The system control circuit 30 is a microcomputer or a sequencer that executes a program, and is connected to a foot switch 6 and a display unit 46 provided outside the diagnostic auxiliary device 3 in addition to the circuits described above. The system control circuit responds to input signals from the foot switch 6, the second A / D converter 43 and the second detector 40, as will be described in detail later with reference to the flowcharts of FIGS. Then, by controlling each of the drivers 43 to 45 and the intensity control circuit 47, a value (ratio) indicating the state of the examination target part is calculated based on the signal obtained from the first A / D converter 42, and calculated The displayed value (ratio) is displayed on the display unit 46. The display unit 46 includes a display device such as a CRT or LCD for displaying a value (ratio) instructed from the system control circuit 30.
[0048]
<Contents Controlled by System Control Circuit 30>
Hereinafter, the processing contents according to the flowcharts of FIGS. 6 and 7 described above by the system control circuit 30 will be described. The process shown in FIG. 6 starts when the main power is turned on to the system control circuit 30.
[0049]
In the first S01 after the start, the system control circuit 30 reads the state of the foot switch 6. The state of the foot switch 6 is on when the foot switch 6 is stepped on by an operator, and is off when the foot switch 6 is not stepped on.
[0050]
In next S02, the system control circuit 30 checks whether the state of the foot switch 6 read in S01 is on or off. If it is off, the system control circuit 30 returns the process to S01.
[0051]
On the other hand, when the state of the foot switch 6 is on, the system control circuit 30 controls the third driver 44 in step S03 to close the purge valve 34 and free up the space in the connector receiver 31. Shut off from the atmosphere.
[0052]
In next step S04, the system control circuit 30 substitutes the digital value input by the second A / D converter 43 (that is, the atmospheric pressure in the connector receiver 31 detected by the pressure sensor 32) into the variable Vps. .
[0053]
In next S05, the system control circuit 30 checks whether or not the value of the variable Vps exceeds a threshold value (for example, “128”). If the value of the variable Vps is less than the threshold, the system control circuit 30 activates the pump 33 by controlling the second driver 45 in S06, and starts exhausting the internal space of the connector receiver 31. After completion of S06, the system control circuit 30 returns the process to S04.
[0054]
On the other hand, if it is determined in S05 that the value of the variable Vps exceeds the threshold value, the system control circuit 30 stops the pump 33 by controlling the second driver 45 in S07.
[0055]
In next S08, the system control circuit 30 executes a measurement process. FIG. 7 is a flowchart showing a measurement processing subroutine executed in S08.
[0056]
In the first S10 after entering this subroutine, the system control circuit 30 instructs the system controller 21 of the light source processor device 2 to turn off the white light source 23, and then instructs the intensity control circuit 47 to turn on the UV lamp 35. At the same time, the rotation filter 37 is rotated at a constant speed by controlling the first driver 43.
[0057]
In the next S11, the system control circuit 30 reads the digital value input from the second detector 40 (that is, a value indicating which region of the rotary filter 37 is inserted in the fluorescence optical path). Substitute into variable Ps.
[0058]
In next S12, the system control circuit 30 checks whether the value of the variable Ps is “1” or “0”. When the value of the variable Ps is “0” (that is, when the λ2 region is inserted in the fluorescence optical path), the system control circuit 30 inputs the first A / D converter 42 in S13. The digital value (that is, the light amount of the fluorescent component having the wavelength λ2 photoelectrically converted by the first detector 38 and amplified by the amplifier 41) is substituted into the variable Vr2. After completion of S13, the system control circuit 30 advances the process to S16.
[0059]
On the other hand, when it is determined in S12 that the value of the variable Ps is “1” (that is, when the λ1 region is inserted in the optical path of fluorescence), the system control circuit 30 in S14 The digital value input by the first A / D converter 42 (that is, the light amount of the fluorescent component having the wavelength λ1 photoelectrically converted by the first detector 38 and amplified by the amplifier 41) is substituted into the variable Vrs. In next S15, the system control circuit 30 substitutes a value obtained by multiplying the value of the variable Vrs by ¼ into the variable Vr1. After completion of S15, the system control circuit 30 advances the process to S16.
[0060]
In S16, it is checked whether or not the values of the variable Vr1 and the variable Vr2 are aligned. If the values of both the variables Vr1 and Vr2 are not yet complete, the CPU 40 returns the process to S11. On the other hand, if the values of both the variables Vr1 and Vr2 are the same, the system control circuit 30 advances the process to S17.
[0061]
In S17, the system control circuit 30 instructs the forced control circuit 47 to turn off the UV lamp 35, then instructs the light source processor device 2 to turn on the white light source 23, and controls the first driver 43 to control the rotation filter. 37 is stopped.
[0062]
In next step S18, the system control circuit 30 substitutes a value obtained by dividing the value of the variable Vr1 by the value of the variable Vr2 into the variable ratio.
[0063]
In next S <b> 19, the system control circuit 30 displays the value of the variable ratio on the display unit 46 as information indicating the state of the examination target part. When S19 is completed, the system control circuit 30 ends this measurement processing subroutine and returns the processing to the main routine of FIG.
[0064]
In the main routine of FIG. 6 in which the process is returned, the system control circuit 30 controls the third driver 44 to open the purge valve 34 and release the internal space of the connector receiver 31 to the atmosphere in S09 after S08. To do. Thereafter, the system control circuit 30 returns the process to S01 and waits for the operator to operate the foot switch 6.
[0065]
<Operation of Embodiment>
The flow of examination using the fluorescence diagnostic system according to the present embodiment configured as described above will be described below.
[0066]
The surgeon inserts the connector 51 of the probe 5 into the connector receiver 31 of the diagnostic auxiliary device 3 in advance. Then, the surgeon starts actual observation with the distal end of the insertion portion 50 of the probe 5 inserted through the forceps channel of the endoscope 1 and slightly protruding from the forceps hole 13.
[0067]
In actual observation, the surgeon inserts the insertion portion of the endoscope 1 into the living body and makes its distal end face a desired site in the living body. Then, a color image 40 of the subject is displayed on the monitor 4. Then, the operator observes the inside of the living body by moving the tip of the endoscope 1 while viewing the color image 40.
[0068]
When a tissue suspected of causing a lesion is found through this observation, a diagnosis using the diagnostic auxiliary device 3 is made. Specifically, the operator brings the tip of the probe 5 into contact with a tissue suspected of causing a lesion and steps on the foot switch 6. As a result, the O-ring 511 is sandwiched between the large-diameter portion of the connector 51 and the flange 310, and the distal end edge of the hood 507 of the insertion portion 50 is brought into close contact with the surface of the subject to be sealed. The space in 31 is exhausted by the pump 33 (S03 to S07). Since the air pressure in the space within the connector receiver 31 is reduced by this exhaust, the space between the distal end surface of the insertion portion 50 and the subject surface sealed by the hood 507 is also exhausted through the suction pipe 503. As a result, the hood 507 is crushed along the shape of the subject surface, and the subject itself is also drawn into the hood 507 so that the distal end surface of the insertion portion 50 and the subject surface are in close contact with each other. The threshold value in S05 described above is set as a value sufficient to bring the distal end surface of the insertion portion 50 into close contact with the subject surface.
[0069]
As described above, when the distal end surface of the insertion portion 50 and the subject surface are in close contact with each other, the distal end of the insertion portion 50 does not deviate from the subject. Therefore, the irradiation of visible light from the light distribution lens 11 of the endoscope is stopped, and the excitation light emitted from the UV lamp 35 is irradiated to the subject through the excitation light guide 501 of the probe 5. (S08, S10). Then, the biological tissue of the measurement target site that is in close contact with the distal end of the insertion portion 50 is excited by the excitation light and emits autofluorescence. A part of the autofluorescence and excitation light is introduced into the diagnostic auxiliary device 3 through the fluorescent light guide 502 of the probe. The diagnostic auxiliary device 3 detects the intensities of the λ1 component and the λ2 component in the fluorescence by the excitation light cut filter 36, the rotation filter 37, and the first detector 38 (S08, S11 to S16), and the λ1 component and λ2 respectively. The intensity ratio of the component is calculated (S08, S18), and the intensity ratio is displayed on the display unit 46 (S08, S19). As described above, since the distal end of the insertion portion 50 is fixed in close contact with the subject surface during this time, the obtained intensity ratio accurately indicates the state of the measurement target portion that is in close contact with the distal end of the insertion portion 50. It is expressed in
[0070]
Thereafter, since the space in the connector receiver 31 is opened to the atmosphere (S09), air flows between the distal end surface of the insertion portion 50 and the subject surface through the suction pipe 503. Thereby, the shape of the hood 507 is restored, and the distal end of the insertion portion 50 can be separated from the subject surface.
[0071]
【The invention's effect】
According to the fluorescence measuring apparatus of the present invention configured as described above, an accurate measurement result can be obtained because the tip of the probe does not deviate from the measurement target site while receiving fluorescence from the subject.
[Brief description of the drawings]
FIG. 1 is a schematic configuration diagram schematically showing a fluorescence diagnostic system according to an embodiment of the present invention. FIG. 2 is a schematic configuration diagram showing a configuration of a diagnostic auxiliary device. FIG. Front view [FIG. 4] Longitudinal sectional view taken along line IV-IV in FIG. 3 [FIG. 5] Front view of the rotary filter [FIG. 6] Flow chart showing a main routine of processing executed by the system control circuit [FIG. FIG. 8 is a flowchart showing a measurement processing subroutine executed in S08 of FIG. 6. FIG. 8 is a graph showing characteristics of excitation light and measurement target light.
DESCRIPTION OF SYMBOLS 1 Electronic endoscope 2 Light source processor apparatus 3 Diagnosis auxiliary apparatus 5 Probe 6 Foot switch 30 System control circuit 31 Connector receptacle 33 Pump 35 UV lamp 35
38 First detector 46 Display unit 50 Insertion unit 51 Connector 501 Excitation light light guide 502 Fluorescence light guide 507 Hood

Claims (5)

In order to analyze the fluorescence generated from the living tissue of the subject by irradiating the subject with excitation light, a fluorescence measurement comprising a long probe and a device main body connected to the proximal end of the probe A device,
The probe is
Incorporating first and second light guides and suction pipes connecting between the front end surface and the apparatus main body,
It comprises a hood made of a cylindrical elastic member that is airtightly attached in a state of surrounding the tip surface with the tip edge protruding beyond the tip surface;
The apparatus main body is
An excitation light source for introducing excitation light into the first light guide;
A light receiving means for receiving the fluorescence guided by the second light guide;
A suction means for performing suction through the suction pipe ;
The probe tip surface surrounded by the hood and the subject surface by sucking air from the tip end surface of the probe through the suction pipe by the suction means with the tip of the hood in close contact with the subject surface The space between the probe and the hood is deformed while keeping in close contact with the subject surface, so that the probe tip surface comes into close contact with the subject surface, and the probe tip is detached from the subject surface. A fluorescence measuring device characterized by preventing . The tip of the probe has a cylindrical shape,
The fluorescence measuring apparatus according to claim 1, wherein the hood has a cylindrical shape and is placed on a tip of the probe. The fluorescence measuring apparatus according to claim 1, wherein the hood is made of rubber. At the base end of the probe, a connector having a columnar shape and the first and second light guides and the base end of the suction pipe are exposed is attached.
The device body is provided with a bottomed cylindrical connector receiver into which the connector is detachably inserted,
The fluorescence measuring apparatus according to claim 1, wherein the suction means sucks a space in the connector receiver that is blocked by the connector. The fluorescence measuring apparatus according to claim 4, wherein a seal member seals between the connector and the connector receiver.

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